Drug delivery device and method of manufacture.
Abstract
Disclosed herein is a wearable drug delivery device including a container filled at least partially with a drug including at least one of a PCSK9 (Proprotein Convertase Subtilisin/Kexin Type 9) specific antibody, a granulocyte colony-stimulating factor (G-CSF), a sclerostin antibody, or a calcitonin gene-related peptide (CGRP) antibody. The wearable drug delivery device may include a needle and an insertion mechanism configured to insert the needle into a patient. A fluid pathway connector may define a sterile fluid flowpath between the container and the insertion mechanism. Optionally, a cannula initially disposed about the needle may be included. The cannula may be retained in the patient at an injection site created by the needle after the needle is withdrawn from the patient. Methods of assembly and operation are also provided.

Term
10.4 yearsleft in the term
Expires 13 February 2037.
- Priority
- Filed
- Granted
- Today
- Expires
27 claims: 7 independent, 20 dependent
- 1NOVEDAD DE LA INVENCIÓN Habiendo descrito la presente invención, se considera como novedad, y por lo tanto se reclama como propiedad lo contenido en las siguientes. REIVINDICACIONES 1. Un dispositivo portátil de administración de fármacos, que comprende:un alojamiento;un recipiente dispuesto en el alojamiento, el recipiente incluye un cuerpo y una junta de émbolo movible a través del cuerpo;un fármaco dispuesto en el cuerpo, el fármaco comprende al menos uno de un anticuerpo específico de Proproteína Convertasa Subtilisina / Kexina de Tipo 9 (PCSK9) o un factor estimulante de colonias de granulocitos (G-CSF);una cánula que tiene un pasaje interno y configurado para estar funcionalmente conectado en comunicación fluida con el recipiente para entregar el fármaco a un paciente durante el uso del dispositivo portátil de administración de fármacos;una aguja introductora inicialmente dispuesta en la cánula y configurada para introducir la cánula en la piel del paciente;un mecanismo de accionamiento dispuesto en el alojamiento y que incluye: una fuente de energía selectivamente activable para mover la junta del émbolo a través del cuerpo: un mecanismo de inserción, que incluye: un miembro de desviación de la inserción retenido inicialmente en un estado activado del miembro de desviación de inserción, el miembro de desviación de la inserción está configurado para mover la aguja introductora y la cánula hacia la piel del paciente a medida que el miembro de desviación de la inserción se desactive, un primer retenedor móvil entre: (i) una posición de retención del primer retenedor, donde el primer retenedor retiene el miembro de desviación de la inserción en el estado activado del miembro de desviación de la inserción y (¡i) una posición de liberación del primer retenedor, donde el primer retenedor permite que el miembro de desviación de la inserción se desactive, un botón dispuesto en una superficie exterior del alojamiento y desplazable manualmente por un usuario;y un ensamblaje de disparo configurado para, en respuesta al desplazamiento del botón por el usuario: (i) activar la fuente de energía para mover la junta del émbolo a través del cuerpo, y (ii) mover el primer retenedor desde la posición de retención del primer retenedor a la posición de liberación del primer retenedor.
- 2El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 1, caracterizado porque el ensamblaje de disparo incluye un primer brazo de control y un segundo brazo de control, el primer brazo de control está configurado para activar la fuente de energía en respuesta al desplazamiento del botón por el usuario, y el segundo brazo de control está configurado para mover el primer retenedor desde la posición de retención del primer retenedor a la posición de liberación del primer retenedor en respuesta al desplazamiento del botón por el usuario. 323
- 3El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 2, caracterizado porque comprende:un sello perforable que controla el acceso a un interior del cuerpo del recipiente;una aguja de acceso al recipiente configurada para perforar el sello perforable para establecer la comunicación fluida entre el recipiente y la cánula durante el uso del dispositivo de fármacos portátil;y un eje de conexión conectado a la aguja de acceso al recipiente y móvil con respecto al recipiente entre: (i) una primera posición del eje de conexión, donde la aguja del acceso del recipiente está separada del sello perforable y (ii) una segunda posición del eje de conexión, donde la aguja de acceso al recipiente perfora el sello perforable.
- 4El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 3, caracterizado porque el primer brazo de control incluye un cuerpo principal y un primero y un segundo salientes que se extienden desde lados opuestos del cuerpo principal, estando configurado el primer saliente para mover el eje de conexión desde la primera posición del eje de conexión a la segunda posición del eje de conexión en respuesta al desplazamiento del botón por parte del usuario, estando configurado el segundo saliente para mover el primer retenedor desde la posición de retención del primer retenedor a la posición de liberación del primer retenedor en respuesta al desplazamiento del botón por parte del usuario.
- 5El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 4, caracterizado porque el desplazamiento del botón por parte del usuario provoca que el ensamblaje de disparo, simultáneamente:(i) active la fuente de energía para mover la junta del émbolo a través del cuerpo, (¡i) mover el primer retenedor desde la posición de retención del primer retenedor a la posición de liberación del primer retenedor y (iii) mover el eje de conexión desde la primera posición del eje de conexión a la segunda posición del eje de conexión.
- 6El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 3, caracterizado porque el ensamblaje disparador incluye:un primer muelle dispuesto entre el botón y el primer brazo de control;un segundo muelle dispuesto en serie con el primer muelle y dispuesto entre el primer brazo de control y el alojamiento;donde el segundo muelle tiene una mayor rigidez que el primer muelle de tal modo que, en respuesta al desplazamiento inicial del botón por el usuario, la compresión inicial del primer muelle es mayor que la compresión inicial del segundo muelle.
- 7El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 1, caracterizado porque comprende:una ventanilla que cubre una abertura en el alojamiento;y el alojamiento incluye una porción del alojamiento superior y una parte del alojamiento inferior, donde la ventanilla está configurada para conectar la parte superior del alojamiento a la parte inferior del alojamiento.
- 8El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 324 1, caracterizado porque el mecanismo de inserción comprende:un miembro de desviación de retracción retenido inicialmente en un estado energizado del miembro de desviación de retracción, el miembro de desviación de retracción está configurado para eliminar el miembro de desviación de retracción del paciente a medida que el miembro de desviación de retracción se desactiva;un segundo retenedor móvil entre: (i) una posición de retención del segundo retenedor, en donde el segundo retenedor retiene el miembro de desviación de retracción en el estado energizado del miembro de desviación de retracción, y (ii) una segunda posición de liberación del segundo retenedor, donde el segundo retenedor permite que el miembro de desviación de retracción se desactive;y el segundo retenedor un clip flexible, donde el clip flexible experimenta deformación elástica cuando el segundo retenedor se mueve desde la posición de retención del segundo retenedor hasta la posición de liberación del segundo retenedor.
- 9El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 1, caracterizado porque comprende:un conducto tubular configurado para estar funcionalmente conectado en comunicación fluida con la aguja de acceso del recipiente durante el uso del dispositivo de administración de fármacos;y un colector que conecta el conducto tubular y la cánula, el miembro de desviación de inserción provoca que el colector y al menos una porción del conducto tubular se muevan con respecto al alojamiento a medida que el miembro de desviación de inserción se desactiva.
- 10El dispositivo portátil de administración de fármacos de conformidad con cualquiera de las reivindicaciones 1 a 9, caracterizado porque comprende:un elemento accionado eléctricamente;una batería configurada para suministrar electricidad al elemento accionado eléctricamente;un adhesivo aplicado a una superficie exterior del alojamiento principal;y un revestimiento adhesivo que cubre el adhesivo, donde la remoción del revestimiento adhesivo del adhesivo causa que la batería suministre electricidad al elemento accionado eléctricamente.
- 11El dispositivo portátil de administración de fármacos de conformidad con cualquiera de las reivindicaciones 1 a 10, caracterizado porque comprende un miembro de calentamiento dispuesto adyacente al conducto tubular y configurado para calentar el fármaco a medida que el fármaco fluye a través del conducto tubular durante la administración.
- 12Un sistema de soporte para un paciente, caracterizado porque comprende:el dispositivo portátil de administración de fármacos de conformidad con la reivindicación 1;el dispositivo portátil de administración de fármacos incluye un primer módulo de comunicación configurado para transmitir un informe representativo de al menos uno de una condición o estado operativo del dispositivo de administración de fármacos;y un dispositivo de proceso de datos externo que comprende: un segundo módulo de comunicación configurado 325 para recibir el informe;un procesador;una memoria acoplada al procesador y configurada para almacenar instrucciones no transitorias ejecutables por ordenador que, cuando son ejecutadas por el procesador, provocan que el procesador: asocie al paciente con al menos un grupo de soporte;almacene, en la memoria, un criterio predefinido para determinar el cumplimiento de un régimen de tratamiento;compare el informe con los criterios predefinidos para determinar si el paciente cumple el régimen de tratamiento;y en respuesta a una determinación de que el paciente no está cumpliendo el régimen de tratamiento, controla el segundo módulo de comunicación para transmitir una comunicación a dicho al menos un grupo de soporte solicitando a dicho al menos un grupo de soporte al menos aconsejar al paciente sobre el régimen de tratamiento.
- 13El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 1, caracterizado porque comprende:un bloqueo que tiene un estado bloqueado en donde la administración del fármaco desde el recipiente está limitada y un estado desbloqueado en donde la administración del fármaco desde el recipiente no está limitada;un sensor de la temperatura;un dispositivo de salida;y un controlador acoplado al bloqueo, al sensor de temperatura y al dispositivo de salida, estando programado el controlador: (a)para determinar si la temperatura de un fármaco dispuesto en el depósito excede un límite superior, y si la temperatura excede el límite superior, activar el dispositivo de salida al menos una vez y colocar el bloqueo en el estado bloqueado;(b) para determinar si la temperatura de un fármaco dispuesto en el depósito está por debajo de un límite inferior y si la temperatura está por debajo del límite inferior, activar el dispositivo de salida al menos una vez y colocar el bloqueo en el estado bloqueado;y c) para determinar si la temperatura del fármaco está entre el límite superior y el límite inferior posterior a (b), y si la temperatura está entre el límite superior y el límite inferior, para colocar el bloqueo en el estado desbloqueado.
- 14El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 13, caracterizado porque comprende:un calentador acoplado al controlador y próximo a por lo menos uno del depósito y el dispositivo de administración de fármacos;y el controlador programado para activar el calentador si la temperatura del fármaco está por debajo del límite inferior, y para desactivar el calentador si la temperatura del fármaco está entre los límites superior e inferior.
- 15El dispositivo portátil de administración de fármacos de conformidad con c la reivindicación 1, caracterizado porque comprende:el mecanismo de accionamiento que incluye un pistón móvil con respecto al alojamiento y configurado para impartir movimiento a la junta del émbolo;y 326 un mecanismo de amortiguación para reducir la velocidad del pistón antes de actuar sobre la junta del émbolo, el mecanismo de amortiguación que comprende un alojamiento del mecanismo de amortiguación, un ensamblaje de pistón móvil en el alojamiento del mecanismo de amortiguación y accionado por el pistón y un fluido de trabajo desplazable por el ensamblaje del pistón para resistir el movimiento del pistón.
- 16El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 6, caracterizado porque comprende:un pistón movible con respecto al alojamiento y configurado para impartir movimiento al sello del émbolo;la fuente de energía que incluye un miembro de desviación del pistón retenido inicialmente en un estado energizado del miembro de desviación del pistón, el miembro de desviación del pistón está configurado para mover el pistón a medida que el miembro de desviación del pistón se desactiva;un tercer retenedor movible entre: (i) una posición de retención del tercer retenedor, donde el tercer retenedor retiene el miembro de desviación del pistón en el estado energizado del miembro de desviación del pistón, y (ii) una posición de liberación del tercer retenedor, donde el tercer retenedor permite que el miembro de desviación del pistón se desactive;y en donde el desplazamiento del botón por el usuario provoca que el ensamblaje de disparo mueva el tercer retenedor desde la tercera posición de retención del tercer retenedor a la posición de liberación del tercer retenedor.
- 17Un método de fabricación de un dispositivo de administración de medicamentos, caracterizado porque comprende:acoplar de manera fluida un recipiente y un mecanismo de inserción de la aguja con un conector de la vía del fluido;esterilizar el conector de la vía de fluido, el recipiente y el mecanismo de inserción de la aguja, por separado o conjuntamente, para crear una trayectoria de flujo del fluido estéril entre el recipiente y el mecanismo de inserción de la aguja;colocar un fármaco en el recipiente después de acoplar de manera fluida el recipiente y el mecanismo de inserción de la aguja con el conector de la vía de fluido, comprendiendo el fármaco un anticuerpo específico de la proproteína convertasa subtilisina/kexina de Tipo 9 (PCSK9) o un factor estimulante de colonias de granulocitos (G-CSF);y disponer el recipiente, el mecanismo de inserción de la aguja y la vía del fluido en un alojamiento del dispositivo de administración de fármacos.
- 18El método de conformidad con la reivindicación 17, caracterizado porque comprende:disponer el recipiente y el mecanismo de inserción de la aguja uno con respecto al otro 327 de tal manera que el recipiente y el mecanismo de inserción de la aguja tengan una primera configuración;y mantener la primera configuración del recipiente y el mecanismo de inserción de la aguja mientras se dispone el anticuerpo específico de PCSK9 o el G-CSF en el recipiente.
- 19El método de la reivindicación 17, caracterizada porque el recipiente y el mecanismo de inserción de la aguja están alineados axialmente en la primera configuración.
- 20El método de conformidad con cualquiera de las reivindicaciones 17 a 19, caracterizado porque comprende:disponer el recipiente y el mecanismo de inserción de la aguja uno con respecto al otro tal que el recipiente y el mecanismo de inserción de la aguja tengan una segunda configuración, diferente de la primera configuración;y mantener la segunda configuración del recipiente y el mecanismo de inserción de la aguja mientras se dispone el recipiente, el mecanismo de inserción de la aguja y la vía del fluido en el alojamiento del dispositivo de administración del fármaco.
- 21El método de conformidad con la reivindicación 20, caracterizado porque el recipiente y el mecanismo de inserción de la aguja no están alineados axialmente en la segunda configuración.
- 22El método de conformidad con cualquiera de las reivindicaciones 18 a 21, caracterizado porque:disponer el recipiente y el mecanismo de inserción de la aguja uno con respecto al otro, tal que el recipiente y el mecanismo de inserción de la aguja tengan la primera configuración, comprende disponer un vehículo alrededor de un perímetro de al menos uno del recipiente o del mecanismo de inserción de la aguja;y disponer el recipiente y el mecanismo de inserción de la aguja uno con respecto al otro, tal que el recipiente y el mecanismo de inserción de la aguja tengan la segunda configuración, comprende retirar el vehículo del al menos uno del recipiente o del mecanismo de inserción de la aguja.
- 23Un dispositivo portátil de administración de fármacos, que comprende:un recipiente que contiene un fármaco, comprendiendo el fármaco al menos uno de un anticuerpo específico de Proproteína Convertasa subtilisina / Kexin tipo 9 (PCSK9) o un factor de estimulación de colonias de granulocitos (G-CSF);un conjunto de sellos conectado al recipiente y que incluye un sello perforable que cubre una abertura formada en una pared del recipiente;y un montaje de conexión de trayectoria del fluido, que incluye un eje de conexión que define una primera cavidad que tiene una condición aséptica, un miembro de perforación que tiene un punto dispuesto en la primera cavidad en una 328 posición inicial y dispuesto a través del sello perforable en el recipiente en una posición de suministro, y un primer sello desplazable que tiene una posición de sellado donde el primer sello desplazable mantiene la condición aséptica de la primera cavidad, y una posición de no sellado donde el primer sello desplazable no mantiene la condición aséptica de la primera cavidad, en donde el primer sello desplazable está configurado para desplazarse desde la posición de sellado a la posición de no sellado por contacto con el conjunto de sellado durante el uso del dispositivo portátil de administración de fármacos.
- 24El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 23, caracterizado porque comprende:una superficie exterior del sello perforable que tiene una condición aséptica;y un segundo sello desplazable que tiene una posición de sellado donde el segundo sello desplazable mantiene la condición aséptica de la superficie exterior del sello perforable, y una posición de no sellado donde el segundo sello desplazable no mantiene la condición aséptica de la superficie exterior del sello perforable.
- 25El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 24, caracterizado porque el segundo sello desplazable está configurado para desplazarse desde la posición de sellado a la posición de no sellado por contacto con el conjunto de conexión de trayectoria del fluido durante el uso del dispositivo portátil de administración de fármacos.
- 26El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 23, caracterizado porque el eje de conexión define una segunda cavidad adyacente a la primera cavidad, el primer sello desplazable incluye un tapón de cierre recibido deslizablemente en la segunda cavidad cuando el primer sello desplazable está en la posición de sellado.
- 27El dispositivo portátil de administración de fármacos de conformidad con la reivindicación 23, caracterizado porque comprende un retenedor que tiene un extremo recibido de forma deslizante en la primera cavidad del eje de conexión, extendiéndose la punta del miembro de perforación hacia fuera desde el extremo del retenedor. 329
Independent claims27
1,272 paragraphs in 9 sections, as filed
(54) Title: PHARMACEUTICAL ADMINISTRATION DEVICE, METHOD OF MANUFACTURE AND METHOD OF USE.
(54) Title: DRUG DELIVERY DEVICE AND METHOD OF MANUFACTURE.
(57) Summary
Disclosed herein is a portable drug delivery device that includes a container at least partially loaded with a drug that includes at least one of a specific antibody to PCSK9 (Proprotein Convertase Subtilisin / Kexin Type 9), a stimulatory factor for granulocyte colonies (G-CSF) sclerostin, or a calcitonin gene-related peptide (CGRP) antibody. The drug portable delivery device may include a needle and an insertion mechanism configured to insert the needle into a patient. A fluid path connector can define a path of sterile fluid flow between the container and the insertion mechanism. Optionally, a cannula initially disposed around the needle may be included. The cannula can be retained in the patient at an injection site created by the needle after the needle is withdrawn from the patient. Assembly and operation methods are also provided.
(57) Abstract
Disclosed herein is a wearable drug delivery device including a container filled at least partially with a drug including at least one of a PCSK9 (Proprotein Convertase Subtilisin / Kexin Type 9) specific antibody, a granulocyte colony-stimulating factor (G-CSF), a sclerostin antibody, or a calcitonin gene-related peptide (CGRP) antibody. The wearable drug delivery device may inelude a needle and an insertion mechanism configured to insert the needle into a patient. A fluid pathway connector may defines a sterile fluid flowpath between the container and the insertion mechanism. Optionally, a cannula initially disposed about the needle may be included. The cannula may be retained in the patient at an injection site created by the needle after the needle is withdrawn from the patient. Methods of assembly and operation are also provided.
DRUG ADMINISTRATION DEVICE, METHOD OF MANUFACTURE AND METHOD OF USE
FIELD OF THE INVENTION
The present disclosure relates generally to drug delivery devices and, more particularly, to a drug delivery device that can be carried by a patient while the drug delivery device delivers a drug to the patient.
BACKGROUND OF THE INVENTION
Parenteral administration of various drugs, that is, administration by different means through the digestive tract, has become a desired method of drug administration for a number of reasons. This form of drug administration by injection can enhance the effect of the substance being administered and ensure that the unchanged drug reaches its intended site at a significant concentration. Similarly, unwanted side effects associated with other routes of administration, such as systemic toxicity, can potentially be avoided through parenteral administration. By bypassing the digestive system of a mammalian patient, degradation of the active ingredients caused by catalytic enzymes in the digestive tract and liver can be avoided, and ensure that a required amount of drug, at a desired concentration, reaches the chosen site.
Traditionally, manually operated syringes and injection pens have been used to administer parenteral drugs to a patient. More recently, parenteral administration of liquid medications into the body has been accomplished by administering bolus injections using a needle and reservoir, continuously by gravity-powered dispensers, or by transdermal patch technologies. Bolus injections often overlap imperfectly with the patient's clinical needs and generally require higher individual doses than desired at the specific time of administration. Continuous administration of medications through gravity feeding systems compromises patient mobility and lifestyle and limits therapy to simplified flow rates and profiles. Another form of drug delivery, transdermal patches, has its similar restrictions. Transdermal patches often require specific drug molecular structures for efficacy and control of drug delivery through a transdermal patch is severely limited.
Ambulatory infusion pumps have been developed to administer liquid medications to a patient. These infusion devices have the ability to deliver sophisticated fluid delivery profiles that meet bolus, continuous infusion, and variable flow delivery requirements. These infusion capabilities generally result in better drug and therapy efficacy and less toxicity to the patient's system. Currently available ambulatory infusion devices are expensive, difficult to program and prepare for infusion, and tend to be bulky, heavy, and very fragile. Filling these devices can be difficult and requires the patient to carry both the prescribed medication and the filling accessories. The devices typically require specialized care, maintenance, and cleaning to ensure adequate functionality and safety for their intended long-term use, and are not cost-effective for patients or healthcare professionals.
Compared to syringes and injection pens, pump-type delivery devices can be significantly more convenient for a patient, in that drug doses can be automatically calculated and administered to a patient at any time during the day or the day. night. Furthermore, when used in conjunction with metabolic sensors or monitors, the pumps can be automatically controlled to provide appropriate doses of a fluid medium at appropriate times of need, based on detected or monitored metabolic levels. As a result, pump-type delivery devices have become an important aspect of modern medical treatments for various types of medical conditions, such as diabetes and the like.
Although pump-type delivery systems have been used to meet a number of patient needs, manually operated syringes and injection pens are often still a preferred choice for drug delivery as they now provide safety features. integrated and can be easily read to identify the status of drug administration and the end of dosing. However, manually operated syringes and injection pens cannot be universally applied and are not preferred for the administration of all drugs. There continues to be a need for an adjustable (and / or programmable) infusion system that is accurate and reliable and can offer clinicians and patients a small, low-cost, lightweight and simple-to-use alternative for parenteral administration of liquid medications.
There is strong demand in the market for drug delivery devices that are easy to use, cost effective, and that include built-in safety features. However, manufacturing such devices can be expensive, resulting in higher costs for patients. Much of the manufacturing cost can be attributed to the need to maintain a sterile fluid path from the drug container to the needle, prior to the introduction of the drug into the patient. Some commercial products seek to maintain the sterility of the device by manufacturing the components in a non-sterile environment, and then by sterilizing the entire device. A recognized drawback of such processes is the need to separately fill the drug container after sterilization of the device, but before injection of the drug, since most pharmaceuticals are not capable of supporting the sterilization process of the drug. device. Alternatively, the drug delivery device can be manufactured as a pre-loaded device, where the device is aseptically loaded with the drug during assembly. Such manufacturing processes can be expensive, since the entire process must be kept sterile and because the loading and assembly ways have to be specially adapted for the device. Consequently, this adds substantial operating costs to pharmaceutical companies and contract drug dispensers.
Drug delivery devices are generally prepared by molding or shaping the various components, and then assembling the components. Assembly steps and other processing operations typically produce a device that must subsequently be cleaned to remove particles that adhere to surfaces to meet cleaning standards for drug delivery devices. After cleaning, conventional drug delivery devices are packaged and sterilized. Such delivery devices have been classified into several general types. The first type is assembled and placed in sterile containers that can be shipped with a vial or ampoule of a drug or other injectable solution. The delivery device is loaded with the drug or other solution at the point of use and injected into the patient. These devices have the disadvantage of increasing the time and difficulty of filling the device at the point of use, increasing the risk of contamination of the delivery device and / or the drug solution, and increasing the probability of accidental drug spills. There is an additional risk of glass particles from the ampoules contaminating the drug solution when the ampoules are opened. In addition, the healthcare professional and / or patient may need training to ensure that the device is properly charged.
Several of these disadvantages are overcome by providing pre-filled delivery devices that can be loaded with a suitable drug solution prior to use. Preloaded delivery devices, as the term is known in the art, are devices that the drug manufacturer charges and sends to the healthcare professional or self-administered patient in a condition that is ready for use. The vial or ampoule is generally made of glass or other transparent material that does not interfere with the stability of the drug during prolonged storage. Pre-filled delivery devices have the advantage of convenience and ease of application with reduced risk of contamination of the drug solution. Prefilled drug delivery devices are generally assembled and packaged in clean rooms to maintain adequate levels of cleanliness. Cleanrooms are equipped with extensive sets of filters and air control systems to remove particulates and pyrogens from the room air and prevent particulates and pyrogens from entering the room. Clean room operators and other personnel should wear appropriate protective clothing to reduce contamination of the air and drug delivery devices that are being manufactured or assembled. As people and equipment enter and leave the clean room, the risk of contamination and introduction of foreign particles and pyrogens increases. Various operations are capable of forming clean and sterile drug delivery devices. However, subsequent handling, loading, and printing of the drug delivery device may contaminate the device. Therefore, it is necessary to clean and sterilize such conventional drug delivery devices before use. Accordingly, there is a continuing need in the industry for an improved system for manufacturing and assembling clean and sterile medical devices and charging such devices.
THE INVENTION
One aspect of the present disclosure provides a portable drug delivery device, including a housing, a container disposed in the housing, a drug disposed in the container, an insertion mechanism disposed in the housing, a fluid line connector defining a flow path for sterile fluid between the container and the insertion mechanism, a needle, and a cannula initially disposed around the needle. The drug may include at least one of: a PCSK9-specific antibody (a proprotein convertase subtilisin / kexin type 9), a granulocyte colony-stimulating factor (G-CSF), a sclerostin antibody, or a gene-related peptide of calcitonin (CGRP). The fluid path connector can include a flexible fluid line. The insertion mechanism may include a wall fixed immovably relative to the housing, a collector guide movable relative to the wall, an insert deflection member initially held in an activated state between the wall and the collector, a shaft connected to the needle, a retraction deflection member initially held in an energized or energized state between the shaft and the manifold, a flexible clip that initially houses the retraction deflection member in the activated state and a collector connected to the collector guide and movable between a first position and a second position. The collector can have an internal chamber and a partition. The cannula and flexible fluid passage can each be in fluid communication with the internal chamber of the manifold. The cannula and flexible fluid conduit can each be connected to the manifold such that the cannula and flexible fluid conduit each move relative to the wall of the insertion mechanism when the manifold is moved between the first position and the second position.
Another aspect of the present disclosure provides a portable drug delivery device that includes a housing, a container disposed in the housing, a drug, a needle, an insertion mechanism, and a fluid path connect defining a flow path. of sterile fluid between the container and the insertion mechanism. The container may include a body, a plunger seal movable through the body, and a pierceable seal. The drug can be disposed in the body of the container. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The insertion mechanism may be configured to move the needle from a retracted position to an inserted position. The fluid path connecting may include a connecting shaft, a piercing member connected to the connecting shaft, and a sterile sleeve having a first end connected to the connecting shaft and a second end connected to the container. The piercing member may initially be retained within the sterile sleeve between the connecting shaft and the pierceable seal of the container.
Yet another aspect of the present disclosure provides a cartridge for assembly in a drug delivery device. The cartridge may include a container having a longitudinal axis, a drug disposed in the container, a needle, an insertion mechanism, and a fluid path connect that defines a path for sterile fluid flow between the container and the mechanism. insertion. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The insertion mechanism may be configured to move the needle from a retracted position to an inserted position. The fluid path connection may have: (i) a first configuration, prior to assembly of the cartridge in the drug delivery device, where the insertion mechanism is aligned with the longitudinal axis, and (ii) a second configuration, after assembly of the cartridge in the drug delivery device, where the insertion mechanism is not aligned with the longitudinal axis.
A further aspect of the present disclosure provides a method of manufacturing a drug delivery device. The method may include: (a) fluidly coupling a container and needle insertion mechanism with a fluid path connect: (b) sterilizing the fluid path connect, container and insert mechanism of the needle, separately or together, to create a path for the flow of sterile fluid between the container and the needle insertion mechanism; (c) disposing a drug in the container after fluidly coupling the container and the needle insertion mechanism with the fluid path connecting; and (d) arranging the container, the needle insertion mechanism and the fluid path in a housing of the drug delivery device. The drug may include at least one of: a PCSK9-specific antibody, a GCSF, a sclerostin antibody, or a CGRP antibody.
Yet another aspect of the present disclosure provides a method of manufacturing a cartridge for a drug delivery device. The method may include: (a) fluidly coupling a container and a needle insertion mechanism with a fluid path connector; (b) sterilize the connecting of the fluid path, the container and the needle insertion mechanism, separately or together, to create a path for the flow of sterile fluid between the container and the needle insertion mechanism; (c) disposing a drug in the container after fluidly coupling the container and the needle insertion mechanism with the fluid path connector. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody.
Another aspect of the present disclosure provides a method of drug delivery. The method may include: (a) providing a portable drug delivery device that includes a container, a needle, and a drug disposed in the container; (b) removably fix a portable drug delivery device to a patient's skin; and (c) activating the portable drug delivery device to insert a pointed end of the needle into the patient to define an injection site and discharge the drug from the container to the patient at the injection site. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody.
A further aspect of the present disclosure provides a method of operating a portable drug delivery device. The method may include: (a) displacing an activation mechanism to disengage one or more locking pins from the corresponding locking windows of an insert mechanism housing, where said decoupling allows an insert deflection member to expand in a direction distal to substantially the same. along a longitudinal axis of the insertion mechanism housing, where said expansion drives the insertion of a needle and a cannula into the body of a patient; (b) decoupling one or more release surfaces of a clip from the coupling with a shaft retained within a manifold guide within the insert mechanism housing, where such decoupling allows a retraction deflection member to expand in a proximal direction substantially along the longitudinal axis of the insertion mechanism housing, where said expansion directs retraction of the needle while retaining the cannula in the patient's body; (c) establishing fluid communication between a fluid path connector having a piercing member and a container having a pierceable seal, where a drug is disposed in the container; and (d) activating an actuation mechanism to force the drug through connecting the fluid path, the cannula, and into the patient's body. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody.
Another aspect of the present disclosure provides a portable drug delivery device that includes a container, a drug disposed in the container, and an actuation mechanism. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The drive mechanism may include: a drive housing having an axial opening, a contact sleeve slidably mounted in the drive housing through the axial opening of the drive housing, a state switch interconnect, a member deviation drive and a piston. The contact sleeve may have a proximal end of the contact sleeve, a distal end of the contact sleeve, and sleeve hooks at the distal end of the contact sleeve. The piston may have a proximal end of the piston, a distal end of the piston, an interface surface, and a contact protrusion near the proximal end of the piston. The sleeve hooks can be made to contact the piston between the interface surface and the contact protrusion during operation of the portable drug delivery device. The drive deflection member may be configured to rest on the interface surface of the piston.
Another aspect of the present disclosure provides a portable drug delivery device that includes a container, a drug, a needle, an insertion mechanism configured to move the needle from a retracted position to an inserted position; and a fluid path connect defining a sterile fluid flow path between the container and the insertion mechanism. The container may include a body, a plunger seal movable through the body, and a pierceable seal. The pierceable seal may include a first internal chamber accessible through a first opening formed in the pierceable seal. The drug can be disposed in the body of the container. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. Fluid path connecting may include: a connecting shaft having a second internal chamber accessible through a second opening formed in the connecting shaft; a first film attached to the connecting shaft to cover the second opening and maintain the sterility of the second internal chamber; a second film attached to the container to cover the first opening and maintain the sterility of the first internal chamber; and a piercing member disposed, at least partially, in the second inner chamber and configured to pierce the first film and the second film in response to activation of the portable drug delivery device.
Yet another aspect of the present disclosure provides a portable drug delivery device that includes a container, a drug disposed in the container, a needle, an insertion mechanism configured to move the needle from a retracted position to an inserted position; and a fluid path connector defining a sterile fluid flow path between the container and the insertion mechanism. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The insertion mechanism includes: a housing having an internal chamber, a cover provided in the internal chamber, a rotational deflection member initially held in an activated state with at least a portion of the rotational deflection member coupled to the housing, a shaft connected to a proximal end of the needle and a retraction deflection member initially held in an activated state between the shaft and the cover.
A further aspect of the present disclosure provides a portable drug delivery device that includes a container, a drug and an actuation mechanism. The container may include a body, a plunger seal configured to move axially within the body, and a pierceable seal. The drug can be disposed in the body of the container. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The drive mechanism may include: an actuator; a set of gears; a piston connected to the piston seal and configured to move axially within the body, a deviation member initially retained in an activated state; and a strap. The deflection member may be configured to expand to impart axial motion to the piston when released from the activated state. The belt may have a first end and a second end connected, respectively, to the piston and the gear assembly. The tether may be configured to restrict the expansion of the deflection member when the deflection member is released from the activated state, such that the strap restricts the axial movement of the piston within the body.
A further aspect of the present disclosure provides a drug delivery device that includes an insertion mechanism, an actuation mechanism, a sterile fluid path, and a drug container comprising a drug. The device may be configured to deliver approximately 2 ml of the drug to a human patient at a flow rate of up to approximately 12 ml per minute. The drug may include at least one of a sclerostin antibody or a calcitonin gene related peptide (CGRP).
Another aspect of the present disclosure provides a drug delivery device that includes a means of delivering a drug to a patient of about 2 ml at a flow rate of up to about 12 ml per minute. The drug includes at least one of a sclerostin antibody or a calcitonin gene-related peptide (CGRP).
Yet another aspect of the present disclosure provides a method of administering a drug, including: (a) contacting a human patient with a drug delivery device configured to deliver approximately 2 ml of a drug at a flow rate of up to approximately 12 ml per minute, where the drug comprises at least one of a sclerostin antibody or a calcitonin gene related peptide (CGRP); and (b) operates the drug delivery device to deliver the drug to the patient.
Another aspect of the present disclosure provides a portable drug delivery device that includes a container, a drug, a needle, a patient-manually operable activation member, an insertion mechanism, a fluid path connect, a set lock and a selector. The drug may be disposed in the container. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The insertion mechanism may be configured to move the needle from a retracted position to an inserted position. The insertion mechanism may be a rotary housing and a rotational deflection member initially held in an activated state. Connecting the fluid path can define a path of sterile fluid flow between the container and the insertion mechanism. The locking assembly may have a locking configuration, where the locking assembly engages the rotary housing to inhibit rotation of the rotary housing, and an unlock configuration, where the locking assembly disengages from the rotary housing to allow rotation of the housing rotary. The selector may have a first configuration, where the selector operatively decouples the activation member and the lock assembly, and a second configuration, where the selector operatively couples the activation member and the lock assembly to allow the activation member change the lock set from lock settings to unlock settings.
A further aspect of the present disclosure provides a portable drug delivery device that includes a main housing, a container, a drug, a window, an introducer needle, a cannula, a drive mechanism, an insertion mechanism, a connection of fluid path, button, and trigger assembly. The container can be arranged in the main housing. The container may include a body, a plunger seal movable through the body, and a first pierceable seal that controls access to the interior of the body. The drug may be disposed in the body. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The window can cover an opening in the main housing. At least a part of the container can be visible through the window. The introducer needle may have a proximal end and a distal end. The cannula may initially be disposed around the distal end of the introducer needle. The drive mechanism can be arranged in the main housing. The drive mechanism may include: a drive housing, a piston movable with respect to the drive housing and configured to impart movement to the piston seal, a piston deflection member disposed between the drive housing and the piston, and a first retainer . The piston deflection member may initially be retained in a piston deflection member in the excited state. The piston bypass member may be configured to move the piston when the piston bypass member is de-energized or deactivated. The first retainer may be movable between: (i) the retention position of the first retainer, where the first retainer retains the piston deflection member in the deviation member activated state and (ii) a first retainer release position, where the first retainer allows the piston bypass member to deactivate. The fluid path connector can define a path of sterile fluid flow between the container and the insertion mechanism. The fluid path connector may include a tubular conduit, a container access needle, and a connecting shaft. The tubular conduit can have one end and a second end. The container access needle may be configured to pierce the first pierceable seal to establish fluid communication between the body and the tubular conduit during drug administration. The connection shaft can be connected to the access needle to the container and to the first end of the tubular conduit. The connecting shaft may have an inner chamber of the connecting shaft that provides fluid communication between the container access needle and the tubular conduit during drug administration. The insertion mechanism can be arranged in the main housing. The insertion mechanism may include an insertion mechanism a manifold, a second pierceable seal, an insert deflection member, a second retainer, an axle, a retraction deviation member and a third retainer. The collector can be mobile relative to the insert mechanism housing. The collector may be connected to the cannula and to the second end of the tubular conduit, the collector having an internal chamber of the collector that provides fluid communication between the tubular conduit and the cannula during drug administration. The second pierceable seal can be connected to the collector and control access to the collector's internal chamber. The distal end of the introducer needle may be provided through the second pierceable seal. The insert deflection member may be disposed between the insert mechanism housing and the manifold.
The insert deflection member may initially be retained in an insert deflection member in the excited state. The insert deflection member may be configured to move the manifold in a distal direction when the insert deflection member is deactivated. The second retainer may be movable between: (i) the retention position of the second retainer, where the second retainer retains the insert deflection member in the energized state of the insert deflection member and (i) a position of releasing the second retainer, where the second retainer allows the insert deflection member to deactivate. The shaft may be connected to the proximal end of the introducer needle. The retraction deflection member may be disposed between the shaft and the manifold. The retraction deviation member may initially be retained in a retraction deviation member in the excited state. The retraction deviation member may be configured to move the shaft in a proximal direction when the retraction deviation member is deactivated. The third retainer may be movable between: (i) a third retainer retention position, where the third retainer retains the retraction bypass member in the energized state of the retraction bypass member and (ii) a third release position retainer, where the third retainer allows the retraction deviation member to deactivate. The button can protrude from the main housing and can be manually moved by a user. The trigger assembly may be configured to, in response to the movement of the button by the user, move: (i) the first retainer from the first retainer retention position to the first retainer release position, and (ii) the second retainer from the retention position of the second retainer to the release position of the second retainer.
Another aspect of the present disclosure provides a portable drug delivery device that includes a main housing, a container, a drug, a window, an introducer needle, a cannula, a drive mechanism, an insertion mechanism, a connector of the fluid path, a button and a trigger set. The container can be arranged in the main housing. The container may include a body, a plunger seal movable through the body, and a first pierceable seal that controls access to the interior of the body. The drug may be disposed in the body. The drug may include at least one of: a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, or a CGRP antibody. The window can cover an opening in the main housing and at least a part of the container can be visible through the window. The introducer needle may have a hollow interior, a proximal end, and a distal end. The drive mechanism can be arranged in the main housing. The drive mechanism may include a drive housing, a piston movable with respect to the drive housing and configured to impart movement to the piston seal, a gear assembly, an electric actuator, a gear interface, a deflection member of the piston and a belt. The electric actuator can rotate the gear interface. Rotation of the gear interface can cause the gear interface to selectively engage the gear assembly to prevent or allow rotation of the gear assembly. The piston deflection member may be disposed between the actuation housing and the piston. The piston deflection member may initially be retained in a piston deflection member in the energized state. The piston bypass member may be configured to move the piston when the piston bypass member is deactivated. The belt can connect at opposite ends to the gear assembly and the piston. The belt may initially retain the piston deflection member in the energized state of the piston deflection member. Rotation of the gear assembly can create slack in the belt allowing the piston bypass member to deactivate. The fluid path connector can define a path of sterile fluid flow between the container and the insertion mechanism. The fluid path connector can include a tubular conduit that has a first end and a second end. The second end of the tubular conduit may be in fluid communication with the hollow interior of the introducer needle during drug administration. The container access needle may be configured to pierce the first pierceable seal to establish fluid communication between the body and the tubular conduit during drug administration. The connection shaft can be connected to the access needle to the container and to the first end of the tubular conduit. The connecting shaft can provide fluid communication between the container access needle and the tubular conduit during drug administration. The insert deflection mechanism may be arranged in the main housing. The insert deflection mechanism may include a base, an insert mechanism housing rotatable relative to the base, a rotational deflection member connected to the insert mechanism housing, a first retainer, a shaft, a deflection member of retraction and a second retainer. The rotational deflection member may initially be retained in an energized state of the rotational deflection member, the rotational deflection member being configured to rotate the insert mechanism housing as the rotational deflection member is deactivated. The first retainer may be movable between: (i) the retention position of the first retainer, where the first retainer retains the rotational deflection member in the energized state of the rotational deflection member and (ii) a release position of the first retainer , where the first retainer allows the rotational deflection member to deactivate. The shaft may be connected to the proximal end of the introducer needle. The shaft may be configured to translate relative to the insert mechanism housing. The retraction deflection member may be disposed between the shaft and the base. The retraction deflection member may have a retraction deflection member in the excited state. The retraction deviation member may be configured to translate the shaft in a proximal direction when the retraction deviation member is deactivated. The second retainer may be movable between: (i) the retention position of the second retainer, where the second retainer retains the retraction bypass member in the activated state of the retraction bypass member and (i) a release position of the second retainer, where the second retainer allows the retraction deflection member to deactivate. The button can protrude from the main housing and can be manually moved by a user. The trigger assembly may be configured to move the first retainer from the first retainer retention position to the first retainer release position in response to movement of the button by the user.
BRIEF DESCRIPTION OF THE DRAWINGS
It is believed that the disclosure will be more fully understood from the following description taken in conjunction with the accompanying drawings. Some of the figures may have been simplified by omitting selected elements in order to more clearly show other elements. Such omissions of elements in some figures are not necessarily indicative of the presence or absence of particular elements in any of the example embodiments, except as may be explicitly delineated in the corresponding written description. Also, none of the drawings is necessarily to scale.
Figure 1A shows an isometric view of a drug delivery device having integrated security insertion mechanisms, in accordance with an embodiment of the present disclosure;
Figure 1B shows an isometric view of the interior components of the drug delivery device shown in Figure 1 A.
Figure 1C shows an isometric view of the bottom of the drug delivery device shown in Figure 1A;
Figure 2A shows an isometric view of the connectors of the patient-initiated fluid path to drug containers, in accordance with one embodiment of the present disclosure;
Figure 2B shows an isometric view of the fluid path connector shown in Figure 2A attached to a drug container.
Figure 3A shows an exploded view of the fluid path connector, exploded along a longitudinal axis A, according to at least one embodiment of the present disclosure;
Figure 3B shows an exploded cross-sectional view of the fluid path connector shown in Figure 3A;
Figure 4A shows a cross-sectional view of the fluid path connector attached to a drug container, as shown in Figure 2B, prior to patient activation.
Figure 4B shows a cross sectional view of the fluid path connector attached to a drug container, as shown in Figure 2B, with the fluid path connected by the patient.
Figure 5A shows an isometric view, from the distal perspective, of a connection shaft, according to an embodiment of the present disclosure;
Figure 5B shows an isometric view, from the proximal perspective, of the connection axis shown in Figure 5A;
Figure 5C shows a transparent view of the connection shaft shown in Figure 5B;
Figure 6A shows an isometric view, from the distal perspective, of a connection shaft, according to another embodiment of the present disclosure;
Figure 6B shows an isometric view, from the proximal perspective, of the connection axis shown in Figure 6A;
Figure 6C shows a transparent view of the connection shaft shown in Figure 6B;
Figure 7A shows an isometric view of an insertion mechanism, according to a first embodiment of the present disclosure;
Figure 7B shows an isometric view of an insertion mechanism, according to another embodiment of the present disclosure;
Figure 8A shows an exploded, exploded view along an axis A of the insertion mechanism shown in Figure 7A;
Figure 8B shows an exploded cross-sectional, exploded view along an axis A of the insertion mechanism shown in Figure 7A;
Figure 9 shows an isometric cross-sectional view of the insert mechanism housing and the insert mechanism manifold guide, in accordance with a first embodiment of the present disclosure;
Figure 10A shows an isometric view of a clip of the insertion mechanism, according to a first embodiment of the present disclosure;
Figure 10B shows an isometric view of the manifold guide shown in
Figure 9;
Figure 10C shows an isometric view of a manifold, a manifold inlet, and a fluid conduit of the insert mechanism, in accordance with a first embodiment of the present disclosure;
Figure 11A shows a cross-sectional view of an insertion mechanism, according to a first embodiment of the present disclosure, in a locked and ready-to-use stage;
Fig. 11B shows a cross sectional view of an insertion mechanism, according to a first embodiment of the present disclosure, in an unlocked and inserted stage; and
Figure 11C shows a cross-sectional view of an insertion mechanism, according to a first embodiment of the present disclosure, in a retracted step for drug delivery;
Figure 12 shows an isometric view of a drive mechanism, according to at least one embodiment of the present disclosure;
Figure 13 shows an exploded view, along an axis A of the drive mechanism shown in Figure 12A;
Figure 14A shows a cross-sectional view of the drive mechanism shown in Figure 12 in an initial inactive state;
Figure 14B shows a cross-sectional view of the drive mechanism shown in Figure 12 in an actuated state;
Figure 14C shows a cross-sectional view of the actuation mechanism shown in Figure 12 in a further actuated state as drug delivery from the mechanism continues;
Figure 14D shows a cross sectional view of the actuation mechanism shown in Figure 12 as the mechanism approaches completion of drug administration;
Figure 14E shows a cross-sectional view of the drive mechanism shown in Figure 12 as the mechanism performs a compliance push to ensure completion of drug administration;
Figure 15 shows an isometric view of a drive mechanism, according to a second embodiment of the present disclosure;
Figure 16 shows an exploded view, along an axis A of the drive mechanism shown in Figure 15;
Figure 17 shows a cross-sectional view of the drive mechanism shown in Figure 15 in an actuated state;
Figure 18 shows an isometric view of the drive mechanism, in accordance with a further embodiment of the present disclosure;
Figure 19A shows a cross-sectional view of the drive mechanism shown in Figure 18 in an initial inactive state;
FIG. 19B shows a cross-sectional view of the actuation mechanism shown in FIG. 18 in an actuated state and as the mechanism approaches completion of drug administration;
Figure 19C shows a cross-sectional view of the actuation mechanism shown in Figure 18 as the mechanism completes drug delivery and triggers an end-of-dose signal;
Figure 20A shows an isometric view of yet another embodiment of a drug delivery device having integrated security insertion mechanisms, in accordance with the teachings of the present disclosure;
Figure 20B is an isometric view of the interior components of the drug delivery device shown in Figure 20A;
Figure 20C shows an isometric view of the bottom of the drug delivery device shown in Figure 20A;
Figure 21 is an isometric view of a drive mechanism, according to the embodiment of Figures 20A-20C;
Figure 22 is an exploded view, along an axis A of the drive mechanism shown in Figure 21;
Figure 23A is a cross sectional view of the drive mechanism shown in Figure 21 in an initial inactive state;
Figure 23B is a cross-sectional view of the drive mechanism shown in Figure 21 in an actuated state;
Figure 23C is a cross-sectional view of the actuation mechanism shown in Figure 21 at the completion of drug administration;
Figure 24A is a cross-sectional view of the drive mechanism taken along line 14-14 in Figure 21; and
Figure 24B is a cross-sectional view of the drive mechanism similar to Figure 24A, but after sensor activation;
Figure 25 is an isometric view of a drug delivery device incorporating an embodiment of a refill-fill cartridge in accordance with aspects of the disclosure;
Figure 26A is a schematic representation of an exemplary refill-refill cartridge of the present disclosure;
FIG. 26B is a graph of example combinations of components of a refill-refill cartridge according to aspects of the disclosure;
Figure 27 is an exploded isometric view of a finished refill cartridge, according to one embodiment of the disclosure;
FIG. 28 is an enlarged fragmentary isometric cross-sectional view of the fluid path connector of the charge-finish cartridge shown in FIG. 27, with shading removed for clarity;
FIG. 29 is an isometric view of the charge-finish cartridge of FIG. 27 prior to insertion of a plunger seal, with the elements of FIG. 29 shown in partial transparency;
Figure 30 is an isometric view of the loading-finishing cartridge of Figure 27 after insertion of a plunger seal, with the elements of Figure 30 shown in partial transparency;
Figure 31 is an exploded isometric view of a tray that can be used to hold a plurality of loading-finishing cartridges for use in a loading-finishing process, with the elements of Figure 7 shown in partial transparency; 31
Figure 32 is an isometric view of the tray of Figure 31 in an assembled form and containing a plurality of load-finish cartridges for use in a load-finish process;
Figure 33 is a side elevation view of another embodiment of a finish-fill cartridge, where the cartridge includes a fully disposable vehicle;
Figure 34 is an exploded view of the refill-finish cartridge of Figure 33;
Figure 35 is a cross-sectional view of the refill-finish cartridge of Figures 33 and 34, shading having been removed for clarity;
Figure 36 is a side elevation view of the refill-finish cartridge of Figures 33-35 with the vehicle removed;
FIG. 37 is an isometric view of a drug delivery device incorporating another embodiment of a refill-fill cartridge in accordance with the disclosure, with a portion of a drug delivery device housing having been removed;
Figure 38 is a side elevational view of the refill-finish cartridge of Figure 37 prior to placement in the housing and including a partially disposable vehicle;
Figure 39 is a cross-sectional view of the refill-finish cartridge of Figure 37, with shading removed for clarity;
Figure 40 is a side elevation view of another embodiment of a refill-finish cartridge in an assembled configuration;
FIG. 41 is a cross-sectional view of the refill-finish cartridge of FIG. 40, with shading removed for clarity;
Figure 42 is a partially exploded view of the finished refill cartridge of Figures 40 and 41, showing a fluid line in the final configuration;
Figure 43 is an exploded view of the fluid path connector of the finish-fill cartridge of Figures 40-42;
FIG. 44 is a cross-sectional view of the finish-fill cartridge of FIG. 40 similar to the view of FIG. 41, but prior to coupling of the fluid path connector to the needle insertion mechanism, shading being removed for the sake of clarity;
Fig. 45 is a side elevation view of another embodiment of a refill-finish cartridge in an assembled configuration;
Figure 46 is a cross-sectional view of the refill-finish cartridge of Figure 41, with shading removed for clarity;
Fig. 47 is a cross-sectional view of the loading-finishing cartridge of Fig. 41 similar to the view of Fig. 42, but prior to coupling of the fluid path connector to the needle insertion mechanism, shading being removed for the sake of clarity;
Figure 48A is an isometric view of one embodiment of a fluid path connection assembly and a drug container in an unassembled configuration;
Figure 48B is an isometric view of the embodiment shown in Figure 48A in an assembled configuration;
Figure 48C is a cross-sectional isometric view of the embodiment shown in Figure 48A in an assembled configuration;
FIG. 49A is an isometric view of one embodiment of a fluid path connection assembly and a drug container in an unassembled configuration;
Figure 49B is an isometric view of the embodiment shown in Figure 49A in an assembled configuration;
Figure 49C is an isometric cross-sectional view of the embodiment shown in Figure 49A in an assembled configuration;
Figure 49D is an isometric cross-sectional view of the embodiment shown in Figure 49A after connection of the fluid path;
Figure 50A is a cross-sectional side view of one embodiment of a fluid path connection assembly and a drug container in an assembled configuration;
FIG. 50B is a cross-sectional side view of the embodiment shown in FIG. 50A after piercing the first and second films;
Figure 50C is a cross-sectional side view of the embodiment shown in Figure 50A after retraction of the external piercing member;
Figure 50D is a cross-sectional side view of the embodiment shown in Figure 50A after connection of the fluid path;
FIG. 51A is a cross-sectional side view of one embodiment of a fluid path connection mechanism and a drug container in an unassembled configuration;
Fig. 51B is a cross-sectional side view of the embodiment shown in Fig. 51A after piercing the first and second films by the external piercing member;
Figure 51C is a cross-sectional side view of the embodiment shown in Figure 51A after connection of the fluid path;
FIG. 52A is a cross-sectional side view of one embodiment of a fluid path connection mechanism and a drug container in an unassembled configuration;
Figure 52B is a cross-sectional side view of the embodiment shown in Figure 52A in an assembled configuration;
FIG. 52C is a cross-sectional side view of the embodiment shown in FIG. 52A after piercing the first and second films by the external piercing member;
Figure 52D is a cross-sectional side view of the embodiment shown in Figure 52A after connection of the fluid path;
FIG. 53A is a cross-sectional side view of one embodiment of a fluid path connection mechanism and a drug container in an assembled configuration;
Figure 53B is a cross sectional side view of the embodiment of Figure 53A after connection of the fluid path;
Figure 54A is a cross sectional side view of one embodiment of a fluid path connection mechanism and a drug container in an unassembled configuration;
Figure 54B is a cross-sectional side view of the embodiment shown in Figure 54A in an assembled configuration;
Figure 54C is a cross-sectional side view of the embodiment shown in Figure 54A after connection of the fluid path;
Figure 55A is a cross-sectional side view of one embodiment of a fluid path connection mechanism and a drug container in an unassembled configuration;
Figure 55B is a cross-sectional side view of the embodiment shown in Figure 55A in an assembled configuration;
Figure 55C is a cross-sectional side view of the embodiment shown in Figure 55A during UV sterilization;
Figure 55D is a cross sectional side view of the embodiment shown in Figure 55A after connection of the fluid path;
Figure 56 shows a fluid line connection according to at least one embodiment of the present disclosure;
Figure 57A shows an isometric view of the interior components of a second embodiment of a drug delivery device;
Figure 57B shows a second view of the interior components of the drug delivery device shown in Figure 57A.
Figure 58A shows an exploded, exploded view along an axis A, of an insertion mechanism according to at least one embodiment of the present disclosure;
FIG. 58B shows an exploded cross-sectional exploded view along an axis A of an insertion mechanism according to at least one embodiment of the present disclosure;
FIG. 59A shows an isometric view of an insert mechanism housing, in accordance with at least one embodiment of the present disclosure;
Figure 59B shows a cross sectional view of the insert mechanism housing shown in Figure 59<sup>to</sup>;
Figure 60 shows an isometric view of an axis according to at least one embodiment of the present disclosure;
Figure 61 shows an isometric view of a sleeve according to at least one embodiment of the present disclosure;
Fig. 62 shows an embodiment of a base of an insertion mechanism, according to at least one embodiment of the present disclosure;
Figure 63A shows an isometric view of an insertion mechanism, according to at least one embodiment of the present disclosure in an initial configuration;
Figure 63B shows a cross-sectional view of an insertion mechanism, according to at least one embodiment of the present disclosure in an initial configuration;
Figure 64A shows an isometric view of an insertion mechanism, according to at least one embodiment of the present disclosure in a needle inserted configuration;
Fig. 64B shows a cross sectional view of an insertion mechanism, according to at least one embodiment of the present disclosure in a needle inserted configuration;
Figure 65A shows an isometric view of an insertion mechanism, according to at least one embodiment of the present disclosure in a needle retracted configuration;
Figure 65B shows a cross sectional view of an insertion mechanism, according to at least one embodiment of the present disclosure in a needle retracted configuration;
Figure 66 shows an isometric view of an insertion mechanism, according to at least one embodiment of the present disclosure;
Figure 67 is a side cross-sectional view of the embodiment of Figure 66;
Figure 68 is a front cross-sectional view of the embodiment of Figure 66;
Figure 69A shows an isometric view of the interior components of a drug delivery device having a multi-function actuation mechanism, in accordance with an embodiment of the present disclosure (shown without the adhesive patch);
Figure 69B shows an isometric view of the interior components of the drug delivery device shown in Figure 69A (shown without the adhesive patch) from another point of view;
Figure 69C shows an isometric view of the interior components of the drug delivery device shown in Figure 69A (shown without the adhesive patch) from yet another point of view;
Figure 69D shows a top view, along axis "A" of the interior components of the drug delivery device shown in Figure 69A;
Figure 70A shows an isometric view of a multi-function actuation mechanism, according to at least one embodiment of the present disclosure prior to activation;
Figure 70B shows an isometric view of a multi-function actuation mechanism, according to at least one embodiment of the present disclosure during activation;
Figure 70C shows an isometric view of a multi-function actuation mechanism, according to at least one embodiment of the present disclosure at a later stage during activation;
Figure 70D shows an isometric view of a multi-function actuation mechanism, according to at least one embodiment of the present disclosure near or at the end of drug administration;
Figures 71A-71D show top views corresponding to the operating steps shown in Figures 70A-70D, respectively;
Figure 72 shows the multi-function actuation mechanism, according to at least one embodiment of the present disclosure, regardless of the drug delivery device;
Figures 73A-73B show the top and bottom views, respectively, of the multifunctional drive mechanism shown in Figure 72;
Figures 73C-73D show the front and rear perspective views, respectively, of the multifunctional drive mechanism shown in Figure 72;
Figure 74 illustrates a top view of one embodiment of an activation mechanism provided in a lower housing of a drug delivery device;
Figure 75 depicts an exploded view of the activation mechanism shown in Figure 74;
FIG. 76A is a cross-sectional view of one embodiment of a fluid path connector and a drug container prior to drug administration;
Figure 76B is a cross-sectional view of the embodiment of a fluid path connector and a drug container of Figure 76A during drug administration;
Figure 76C is a cross sectional view of the embodiment of a fluid path connector and drug container of Figure 76A after completion of drug administration;
FIG. 77 is a schematic illustration of a drug delivery device including a temperature monitoring system, in accordance with an embodiment of the present disclosure;
Figure 78A illustrates an embodiment of an adhesive patch for a drug delivery device constructed in accordance with the principles of the present disclosure;
Figure 78B illustrates an embodiment of an adhesive patch for a drug delivery device constructed in accordance with the principles of the present disclosure;
FIG. 79 depicts an embodiment of a non-adhesive patch liner in combination with a drug delivery device constructed in accordance with the principles of the present disclosure;
Figure 80A illustrates an exploded assembly view of one embodiment of an adhesive patch for a drug delivery device constructed in accordance with the principles of the present disclosure;
Figure 80B depicts the adhesive patch of Figure 80A in assembled form;
Figure 81 illustrates an isometric view of a drug delivery device including an adhesive patch with reinforcing members, in accordance with one embodiment of the present disclosure;
Figure 82 illustrates a bottom view of one embodiment of a non-adhesive patch liner;
Figures 83A-83C illustrate a process of attaching the drug dispensing device of Figure 81 to the skin of a patient;
Fig. 84 is a schematic diagram of a drug delivery device in communication with a data processing network in accordance with an embodiment of the present disclosure;
Figures 85A-85C are schematic diagrams illustrating the operation of an energy management system in accordance with an embodiment of the present disclosure;
Figures 86A-86C are schematic diagrams illustrating the operation of an energy management system in accordance with another embodiment of the present disclosure;
Figures 87A-87C are schematic diagrams illustrating the operation of an energy management system in accordance with another embodiment of the present disclosure;
Fig. 88 is an isometric view of an energy management system in accordance with another embodiment of the present disclosure;
FIG. 89 is an isometric view of an energy management system in accordance with another embodiment of the present disclosure;
FIG. 90 is a cross sectional view of an energy management system in accordance with another embodiment of the present disclosure;
Figures 91A-91B are cross-sectional views illustrating the operation of an energy management system in accordance with another embodiment of the present disclosure;
Figure 92 is a bar graph showing administration times, in seconds (y-axis), for various types of administration (y-axis). TsubQ = administration time, subcutaneous administration (sc), with tolerance to viscosity (case 1); tsubQvc = administration time, subcutaneous administration, constant viscosity (case 2); Tamb = administration time, environmental administration, with viscosity tolerance (Case 3); and tambvc = administration time, environmental administration, constant viscosity (case 4). The error bars show the min / max error;
Fig. 93 is a graph showing the force profiles of the drive system as a function of the drive assembly force (N) (x axis) over the displacement distance (mm) (y axis). In Figure 93, the line with squares indicates a minimum, the line with triangles indicates a maximum, and the lines with diamonds indicate a nominal value;
Figure 94 is a bar graph that transmits the contribution (%) to the variation of the administration time of the components (x-axis) in subcutaneous case 1, sc administration and the viscosity interval. The y-axis shows the relative time contribution as a percentage in seconds;
Figure 95 is a bar graph that transmits the contribution (%) to the variation of the administration time of the components (x-axis) in case 2, sc administration and the viscosity constant. The relative contribution, in seconds, is shown as a percentage on the y axis;
Figure 96 is a bar graph that transmits the contribution (%) to the variation of the administration time of the components (x-axis) in case 3, environmental administration and viscosity interval. The relative contribution, in seconds, is shown as a percentage on the y axis;
Figure 97 is a bar graph that transmits the contribution (%) to the variation of the administration time of the components (x-axis) in case 4, environmental administration and the viscosity constant. The relative contribution, in seconds, is shown as a percentage on the y axis;
Figure 98 is a bar graph that transmits the contribution (%) to the variation of the administration time of the components (x-axis) in case 4, environmental administration and the viscosity constant by variable groups. The relative contribution, in seconds, is shown as a percentage on the y axis;
Figure 99 is a bar graph that transmits the contribution (%) to the variation of the administration time of the components (x-axis) in the administration sc
Figure 100A is an exploded view of an insertion mechanism, according to a first embodiment of the disclosure;
FIG. 100B is an exploded cross-sectional view of the insertion mechanism of FIG. 100A.
Fig. 101 is an isometric view of an insert mechanism housing, in accordance with at least one embodiment of the present disclosure;
Fig. 102 is an isometric view of a cover of the insert mechanism housing, in accordance with at least one embodiment of the present disclosure;
Fig. 103 is an isometric view of a clip according to at least one embodiment of the present disclosure;
Fig. 104 is an isometric view of a clip retainer in accordance with at least one embodiment of the present disclosure;
Fig. 105 is an isometric view of a manifold guide according to at least one embodiment of the present disclosure;
Fig. 106 is an isometric view of a manifold and a fluid line in accordance with at least one embodiment of the present disclosure;
Fig. 107 is an isometric view of a displacement limiter according to at least one embodiment of the present disclosure;
FIG. 108A is an isometric view of a needle insertion mechanism in an initial configuration or initial locked configuration, in accordance with at least one embodiment of the present disclosure;
Fig. 108B is a cross-sectional view of the needle insertion mechanism of Fig. 108<sup>to</sup>;
Figure 109A is an isometric view of the needle insertion mechanism of Figure 108A in a delivery configuration;
FIG. 109B is a cross-sectional view of the needle insertion mechanism of FIG. 108A in a delivery configuration;
Figure 110A is an isometric view of the needle insertion mechanism of Figure 108A in a retracted or unlocked configuration;
Figure 110B is a cross-sectional view of the needle insertion mechanism of Figure 110A in a retracted or unlocked configuration;
Figure 111A is an exploded view of an insertion mechanism, according to a second embodiment of the disclosure;
Figure 111B is an exploded cross-sectional view of the insertion mechanism of Figure 111<sup>to</sup>;
Figure 112 is an isometric view of an insert mechanism housing, in accordance with at least one embodiment of the present disclosure;
Fig. 113 is an isometric view of a manifold guide according to at least one embodiment of the present disclosure;
Fig. 114 is an isometric view of a displacement limiter of at least one embodiment of the present disclosure;
Figure 115A is a cross-sectional view of a needle insertion mechanism in an initial configuration or initial locked configuration, in accordance with at least one embodiment of the present disclosure;
Figure 115B is a cross-sectional view of the needle insertion mechanism of Figure 115A in a delivery configuration;
Figure 115C is a cross-sectional view of the needle insertion mechanism of Figure 115A in a retracted or unlocked configuration;
Fig. 116 is an isometric view of a needle retraction release mechanism of at least one embodiment of the present disclosure;
Fig. 117 is an isometric view of a pivot of at least one embodiment of the present disclosure.
Figure 118 shows an isometric view of a drug container according to at least one embodiment of the present disclosure;
Figure 119 shows an isometric view of a drug container and a fluid path connection in accordance with at least one embodiment of the present disclosure;
Figure 120A shows an isometric view of the drug container and fluid path connection of Figure 119 in a disassembled configuration;
Figure 120B shows an isometric cross-sectional view of the drug container and fluid path connection of Figure 119 in an initial mounted configuration;
Figure 120C shows an isometric cross-sectional view of the drug container and fluid path connection of Figure 119 in an intermediate mounted configuration;
Figure 120D shows an isometric cross-sectional view of the drug container and fluid path connection of Figure 119 in an assembled configuration;
Figure 121A shows an isometric view of one embodiment of a drug container and fluid path connection in an unassembled configuration;
Figure 121B shows a cross-sectional isometric view of the drug container and fluid path connection of Figure 121A in an assembled configuration;
Fig. 122 shows a detailed cross-sectional view of a fluid path in accordance with at least one embodiment of the present disclosure;
FIG. 123 shows an isometric cross-sectional view of one embodiment of a drug container and fluid path connection in an unassembled configuration;
Figure 124 shows an isometric view of one embodiment of a drug container and fluid path connection in an unassembled configuration;
Figure 125 shows a cross sectional view of one embodiment of a drug container and fluid path connection in an unassembled configuration;
Figure 126 shows an isometric cross-sectional view of one embodiment of a drug container and fluid path connection in an unassembled configuration;
Figure 127A shows an isometric view of one embodiment of a drug container and fluid path connection in an unassembled configuration;
Figure 127B shows an end view of a drug container;
Figure 127C shows a cross sectional view of a drug container and fluid path connection in an unassembled configuration;
Figure 127D shows a cross sectional view of a drug container and fluid path connection in a connected configuration;
Fig. 128A shows an exploded view of a medical device with an integrated stimulant source according to at least one embodiment of the present invention;
Fig. 128B shows the medical device of the embodiment of Fig. 128A applied to a patient's skin and the activated stimulant source;
Fig. 128C shows the medical device of the embodiment of Fig. 128A after removing the skin from the patient;
FIG. 129A shows an exploded view of a medical device with an external stimulant source in accordance with at least one embodiment of the present invention;
Fig. 129B shows the medical device of the embodiment of Fig. 129A applied to the patient's skin;
Fig. 129C shows the medical device of the embodiment of Fig. 129A after removal of the medical device from the body and the activated stimulation source;
Figure 129D illustrates removal of the adhesive from the patient's skin;
Figure 130 illustrates an isometric view of the interior components of the drug delivery device 10 (shown without the adhesive patch) installed with one embodiment of the fluid restriction mechanism;
Figure 131A shows an isometric view of a fluid restriction mechanism, according to at least one embodiment of the present invention, attached to an integrated sterile fluid path connection and a drug container;
Figure 131B shows an exploded isometric view of the fluid restriction mechanism and an integrated sterile fluid path connection and a drug container, shown in Figure 131A;
Figure 131C shows a side view of the fluid restriction mechanism shown in Figure 131 A;
Figure 132A shows an isometric view of a fluid restriction mechanism, in accordance with another embodiment of the present invention, attached to a sterile fluid path connection that may or may not be integrated within the drug container;
Figure 132B shows an exploded isometric view of the fluid restriction mechanism and a connection of the sterile fluid path and a drug container, shown in Figure 131A;
Figure 132C shows a side view of the fluid restriction mechanism shown in Figure 132A;
Figure 133A shows an exploded isometric view of the fluid restriction mechanism shown in Figures 131A-131C;
Figure 133B shows another angle of the exploded isometric view of the fluid restriction mechanism shown in Figure 133A;
Figure 133C shows a cross sectional view of the fluid restriction mechanism shown in Figures 133A-4B;
Figure 134A shows an exploded isometric view of a configurable fluid restriction mechanism, in accordance with another embodiment of the present invention;
Figure 134B shows a side view of the configurable fluid restriction mechanism shown in Figure 134A;
Figure 135A shows an isometric view of a stackable fluid restriction mechanism, in accordance with another embodiment of the present invention;
Figure 135B shows an exploded isometric view of the stackable fluid restriction mechanism shown in Figure 135A;
Figure 136A shows an isometric view of a fluid restriction mechanism, in accordance with a further embodiment of the present invention;
Figure 136A shows an isometric view of a fluid restriction mechanism shown in Figure 136A, with the top component of the fluid restriction mechanism removed;
Figure 137A shows an isometric view of a collector having a vent according to a first embodiment of the present disclosure;
Fig. 137B shows an isometric view of the components shown in Fig. 137A, rotated to show the manifold, a manifold inlet, and an insertion mechanism fluid passage, in accordance with a first embodiment of the present disclosure;
Figure 138A shows a cross-sectional view of an insertion mechanism having a vented fluid path, according to a first embodiment of the present disclosure, in a locked and ready-to-use stage;
Figure 138B shows a cross-sectional view of an insertion mechanism having a vented fluid path, according to a first embodiment of the present disclosure, as the fluid passes through a conduit and into the manifold;
Fig. 138C shows a cross sectional view of an insertion mechanism having a vented fluid path, according to a first embodiment of the present disclosure, as the fluid fills the manifold and pushes the gas through the permeable membrane;
Figure 138D shows a cross sectional view of an insertion mechanism having a vented fluid path, according to a first embodiment of the present disclosure, in an inserted and unlocked stage;
Fig. 138E shows a cross-sectional view of an insertion mechanism having a vented fluid path, according to a first embodiment of the present disclosure, in a partially retracted stage as fluid begins to exit the collector through cannula;
FIG. 138F shows a cross-sectional view of an insertion mechanism having a ventilated fluid path, according to a first embodiment of the present disclosure, in a retracted stage for drug delivery;
Figures 139A-139C show cross-sectional views of an insertion mechanism having a ventilated fluid path, in accordance with another embodiment of the present disclosure, as it progresses through the various stages of inserting, ventilating, and administering the drug;
Figure 140A is an isometric view of a connection of the integrated sterile fluid pathway and a drug container, according to one embodiment; and Figure 140B is an isometric sectional view of the integrated sterile fluid path connection and drug container shown in Figure 140A;
Figure 141A is an exploded side view of the components of an embodiment of an integrated sterile fluid path connection and drug container, exploded along a longitudinal axis; and FIG. 141B is an exploded sectional view of the embodiment of FIG. 141.<sup>to</sup>;
Figure 142A is a sectional view of an integrated sterile fluid path connection and a drug container, as shown in Figure 140A, prior to user activation; Figure 142B is a sectional view of the embodiment with the fluid path connected; and FIG. 142C is a sectional view of the embodiment at the end of drug administration;
Figure 143A is an isometric perspective view of the integrated sterile fluid path connection in accordance with one embodiment of the present invention; and FIG. 143B is an exploded perspective view of the components of the integrated sterile fluid path connection shown in FIG. 143A;
FIG. 144A is a sectional view of an embodiment of an integrated sterile fluid path connection, having a piercing member guide and a drug container, prior to activation by the user; Figure 144B shows an isometric perspective view of the guide of the piercing member and the piercing member of the embodiment shown in Figure 144A; and FIG. 144C is an isometric view of the guide of the piercing member, the piercing member and the connecting shaft of the embodiment of FIG. 144A;
Fig. 145 is a cross sectional view of a connection of the integrated sterile fluid pathway and a drug container according to an embodiment prior to user activation, where the drug container comprises more than one drug chamber, each drug chamber separated from the next by a perforable membrane;
FIG. 146A to FIG. 146E are sectional views of one embodiment of a sterile fluid connector where the pierceable seal is configured to maintain different positions within the connector in response to pneumatic and / or hydraulic pressure;
Fig. 147A to Fig. 147H are sectional and isometric sectional views of one embodiment of a sterile fluid connector where the pierceable seal, in response to pneumatic and / or hydraulic pressure, couples or decouples a sensor mechanism that is capable of transmitting a signal indicating the state of fluid transfer from the sterile fluid container to the connector;
Figure 148A to Figure 148G are perspective and sectional views of another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector;
Fig. 149A to Fig. 149D are cross-sectional and cross-sectional isometric views of another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector, showing more specific configurations. of a sensor in the open and closed positions;
FIG. 150A to FIG. 150D are perspective and cross-sectional views of one embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector, illustrating the positions without pressure. (Figure 150B), pressurized (Figure 150C) and end of administration (Figure 150D) of the components of a sterile fluid connector;
Fig. 151A to Fig. 151C are perspective and sectional views of another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector;
Figure 152A is a cross-sectional view and Figure 152B is a cross-sectional isometric view of another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector;
Figure 153A and Figure 153B are cross-sectional isometric views of another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector, where the pierceable seal comprises a material. conductive or cladding;
FIG. 154 is a cross-sectional isometric view of another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector, where the signal is mediated using a conductive elastomeric film. ;
Figure 155 is a cross-sectional isometric view of another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector, where the signal is mediated using a dome switch. ;
Fig. 156 is an isometric view of a drive mechanism, in accordance with yet another embodiment of the present invention;
Figure 157A is a cross-sectional view of the drive mechanism taken along line 15-15 in Figure 156; and
Fig. 157B is a cross-sectional view of the drive mechanism similar to Fig. 157A, but after activation of the sensor.
DETAILED DESCRIPTION OF THE INVENTION
The present disclosure provides drug delivery devices having advantageous insertion mechanisms, actuation mechanisms, sterile fluid path assemblies, status indicators, safety features, and other advantageous components. Such drug delivery devices are safe and easy to use, and are aesthetically and ergonomically attractive to self-administered patients. The drug delivery devices described herein incorporate features that make activating, operating, and blocking the drug delivery device easy even for untrained patients. The drug delivery devices of the present disclosure provide these desirable features without the various problems associated with devices known in the prior art. Furthermore, the sterile fluid path assemblies of the present disclosure can be loaded with pharmaceutical treatments using standard loading equipment and systems. This advantage is enabled by the charge-finish cartridges of the present disclosure which function to maintain the sterility of fluid path assemblies and allow removable nesting, mounting, or otherwise inserting into trays for standard loading processes. -finish, as discussed in more detail below.
As described in more detail below, the drug delivery devices of the present disclosure may contain a drug, which may also be referred to as a medication or a drug. The drug may be, but is not limited to, various biologics (eg, peptides, peptibodies, or antibodies), biosimilars, large molecule drugs (eg, a drug with a molecular weight greater than or equal to about 900 Daltons ), small molecule drugs (for example, a drug with a molecular weight less than or equal to about 900 Daltons), high viscosity drugs, low viscosity drugs, drugs exhibiting characteristics of non-Newtonian fluids such as shear thinning and / or drugs exhibiting characteristics of Newtonian fluids. The drug may be in fluid or liquid form, although the disclosure is not limited to a particular state (eg, no differentiation is intended between a solution, a gel, or a lyophilized product, for example).
A perceived disadvantage of certain known drug delivery devices is their inability to administer highly viscous drugs, such as certain biologics in a timely manner and / or with little discomfort to the patient. High-viscosity drugs typically require more time for injection than low-viscosity drugs. Patients may find it difficult and / or undesirable to hold an autoinjector or syringe against their skin for the amount of time necessary to inject a high-viscosity drug. While the injection time can be decreased by increasing the force of the drive mechanism, a more powerful drive mechanism increases the risk of breakage of the drug container and other internal components of the device. Additionally, a more powerful drive mechanism increases the possibility that the patient will experience an impulse or mechanical shock wave that may disturb or surprise the patient. As a result, the patient may attempt to pull the drug delivery device from the skin, which may compromise full dosing.
Long injection times are more likely to be tolerated by patients if the drug is administered through a drug delivery device that they may carry. Unlike a syringe or auto-injector, the patient does not need to keep a drug delivery device on during drug delivery. Therefore, the patient can resume physical activities after the portable drug delivery device has been placed on the skin and started or otherwise has not been charged while keeping the drug delivery device in its place.
However, certain aspects of portable drug delivery devices have discouraged their adoption in the field of high-viscosity drugs. In order to achieve a compact design with a low profile that does not protrude significantly from the patient's body, portable drug delivery devices often include a drug container that is offset and orthogonal to an insertion mechanism. This arrangement usually requires a tubular conduit with one of more turns to fluidly couple the drug container and the insertion mechanism. Therefore, compared to syringes and auto-injectors, the internal fluid flow path of portable drug delivery devices tends to be relatively long and tortuous.
For drugs that behave like Newtonian fluids (that is, fluids for which the shear rate is directly proportional to the flow rate), a longer flow path may result in a slower flow rate. Thus, portable drug delivery devices, due to their long internal flow paths, have the potential to exacerbate the injection problems associated with high-viscosity drugs. The force of the drive mechanism can be increased to compensate for the reduction in flow rate, but a more powerful drive mechanism increases the risk of drug container breakage and is therefore typically considered undesirable. For at least these reasons, some have observed that drug delivery devices are not particularly suitable for delivering high-viscosity drugs.
The inventors of the present disclosure have discovered that various high-viscosity drugs (eg, PCSK9-specific antibodies, sclerostin antibodies, and G antibodies) exhibit non-Newtonian fluid characteristics when injected through a portable drug delivery device. . One such feature is shear thinning, which is the ability of non-Newtonian fluids to show decreased viscosity when subjected to shear deformation. Shear thinning reduces the viscosity of a fluid as it is pushed through a conduit. Consequently, the force required to push the fluid through a conduit is less than it would be if the fluid were Newtonian. In the context of portable drug delivery devices, shear thinning mitigates the obstructing effect of the device's long internal flow path. Therefore, an unexpected benefit of the portable drug delivery devices found by the inventors of the present disclosure is that they are suitable for delivering high-viscosity drugs that have non-Newtonian characteristics, such as shear thinning. The inventors of the present disclosure found that shear thinning often occurs in drugs such as biologics, which have relatively large protein molecules with a molecular weight greater than or equal to about (eg ± 10%) 900 daltons. Any of the portable drug delivery devices described herein can have a drug container filled with a high-viscosity drug that has shear thinning capabilities and therefore realizes the unexpected benefits of shear thinning in the operation and use of the device.
Some non-limiting embodiments of the drug delivery device and its respective components will now be described with reference to the accompanying figures.
As used herein to describe actuation mechanisms, insertion mechanisms, fluid path connectors, drug delivery devices, or any of the relative positions of the components of the present disclosure, the terms " axially "or" axially "generally refers to a longitudinal axis A around which a component is preferably positioned, although not necessarily symmetrically around it. The term radial generally refers to a direction normal to the A axis. The terms "proximal", "posterior", "posterior", "dorsal" or posterior generally refer to an axial direction in the "P" direction. The terms distal, frontal, forward, depressed, or forward generally refer to an axial direction in direction D. As used herein, the term glass should be understood to include other similar non-reactive materials suitable for use in a pharmaceutical grade application that would normally require glass, including, but not limited to, certain non-reactive polymers such as cyclic olefin copolymers (COC) and cyclic olefin polymers (COP). The term plastic can include both thermoplastic and thermosetting polymers. Thermoplastic polymers can be softened to their original state with heat; thermosetting polymers cannot. As used herein, the term "plastic" refers primarily to moldable thermoplastic polymers such as, for example, polyethylene and polypropylene, or an acrylic resin, which typically also contain other ingredients such as healing agents, fillers, reinforcing agents, colorants and / or plasticizers, etc., and which can be formed or molded under heat and pressure. As used herein, the term plastic is not intended to include glass, nonreactive polymers, or elastomers that are approved for use in applications where they are in direct contact with therapeutic fluids that can interact with plastic or that can be degraded by substituents that, otherwise, they could enter the liquid from the plastic. The term elastomer or elastomeric material primarily refers to crosslinked thermosetting rubber polymers that are more easily deformable than plastics but are approved for use with pharmaceutical grade fluids and are not readily susceptible to leaching or gas migration at temperature and pressure. environmental. As used herein, fluid refers primarily to liquids, but may also include suspensions of solids dispersed in liquids and dissolved gases, or otherwise present with liquids within the fluid-containing parts of delivery devices. of drugs. In accordance with various aspects and embodiments described herein, reference is made to a diversion member, such as in the context of one or more diversion members for insertion or retraction of the needle, trocar, and / or cannula. It will be appreciated that the deflection member can be any element that is capable of storing and releasing energy. Non-limiting examples include a spring, such as, for example, a coil spring, a compression or extension spring, a torsion spring and a leaf spring, a compressible or elastic elastic band, or any other functional member. Similar. In at least one embodiment of the present disclosure, the deflection member is a spring, preferably a compression spring. Also, as used herein, the term "drug delivery device" is intended to include any number of devices that are capable of dispensing a fluid to a patient upon activation. Such drug delivery devices include, for example, portable drug delivery devices, body injectors, out-of-body injectors, auto-injectors, infusion pumps, bolus injectors, and the like. Additionally, as used herein, the term portable drug delivery device is intended to include any number of devices that are capable of dispensing fluid to a patient upon activation and that can be attached to the patient's skin or clothing . Such portable drug-carrying devices include, for example, injectors in the body and injectors outside the body.
L_ Drug Administration Device
Figures 1A-1C show an example of a drug delivery device 10 according to at least one embodiment of the present disclosure. Drug delivery device 10 can be used to administer the delivery of a drug treatment to a patient's body. As shown in Figures 1A-1C, the drug delivery device 10 includes a housing 12. Housing 12 may include one or more subcomponents of the housing that can be attached as a gear to facilitate manufacture, assembly, and operation of drug delivery device 10. For example, drug delivery device 10 includes housing 12, which includes an upper housing 12A and a lower housing 12B. The drug delivery device 10 may further include an activation mechanism 14, a status indicator 16, and a window 18. Window 18 may be any translucent or transmitting surface through which the operation of the drug delivery device can be seen. Drugs 10. In at least one embodiment, window 18 may be configured to connect and hold upper housing 12A and lower housing 12B together. As shown in FIG. 1B, the drug delivery device 10 further includes an assembly platform 20, a sterile fluid line 30, a drive mechanism 100 having a drug container 50, an insertion mechanism 200, a connect the fluid path 300 and a supply and control system 400.
One or more of the components of the drug delivery device 10 can be modular in that, for example, they can be pre-assembled as separate components and configured in place on the mounting platform 20 of the drug delivery device 10 during the making.
Housing 12 may contain some or all of the components of the device. In some embodiments, housing 12 can provide a means for removably attaching drug delivery device 10 to the patient's skin or clothing, making drug delivery device 10 a drug delivery device. portable. In some embodiments, a layer of adhesive can be applied to an outer surface of housing 12, such as the surface through which a cannula protrudes during operation, to fix the drug delivery device 10 removably attached to the skin of a patient.
Housing 12 also provides protection to the interior components of drug delivery device 10 against environmental influences. Housing 12 is ergonomically and aesthetically designed in size, shape, and related features to facilitate easy packaging, storage, handling, and use by patients who may not have undergone training and / or are physically disabled. Furthermore, the outer surface of housing 12 can be used to provide product labeling, safety instructions, and the like. Additionally, as described above, housing 12 may include certain components, such as status indicator 16 and window 18, that can provide the patient with operational information.
Container 50 may be configured to hold a variety of different drug dose volumes, including drug dose volumes in a range of approximately (eg, ± 10%) 0.5-20 ml, or 1-10 ml, or 2 - 10 ml, or 2 - 8 ml, or 2 6 ml, or 2 - 4 ml, or 0.5 - 2 ml, or 0.5 - 1 ml, or 3.5 ml. Container 50 can be completely or partially filled with the drug.
In at least one embodiment, the drug delivery device 10 provides an activation mechanism that the patient displaces to activate a start command to a control feeding system 400. In a preferred embodiment, the trigger mechanism is a start button 14 that is located through housing 12, such as through an opening between upper housing 12A and lower housing 12B, and which contacts a control arm 40 of the supply and control system 400. In at least one embodiment, the start button 14 may be a push button and, in other embodiments, it may be an on / off switch, a toggle switch, or any similar activation feature known in the art. Housing 12 also provides a status indicator 16 and a window 18. In other embodiments, one or more of trigger mechanism 14, status indicator 16, window 18, and combinations thereof may be provided in upper housing 12A or housing 12B, such as, for example, on one side Visible to the patient when drug delivery device 10 is placed on the patient's body. Housing 12 is described in more detail hereinafter with reference to other components and embodiments of the present disclosure.
Drug delivery device 10 may be configured such that upon activation by a patient by depression of the trigger mechanism, drug delivery device 10 is initiated to: insert a fluid pathway into the patient; allow, connect, or open the necessary connections between a drug container, a fluid path, and a sterile fluid line; and forcing the drug fluid stored in the drug container through the fluid path and the fluid line for administration to a patient. For example, one or more optional safety mechanisms can be used to prevent premature activation of the drug delivery device 10. For example, an optional sensor can be provided in body 24 (shown in Figure 1C) in one embodiment as a safety device to ensure that power and control system 400, or trigger mechanism, cannot be attached unless that the drug delivery device 10 is in contact with the patient's body. In one such embodiment, the sensor 24 in the body is located in the lower part of the lower housing 12B, where it can contact the body of the patient. Upon displacement of the sensor 24 in the body, depression of the trigger mechanism is allowed. Accordingly, in at least one embodiment, the sensor 24 in the body is a mechanical safety mechanism, such as, for example, a mechanical lock, that prevents the drug delivery device 10 from being triggered by the activation mechanism 14. In another embodiment, the sensor in the body may be an electromechanical sensor, such as a mechanical lock that sends a signal to the power and control system 400 to enable activation. In still other embodiments, the sensor in the body may be electrically based such as, for example, a sensor based on capacitance or impedance that the tissue must detect before allowing activation of the power or control system 400. In al Minus one embodiment, such an electrically based body sensor can incorporate a resistance with an impedance of approximately (eg, ± 10%) 1 ΜΩ. These concepts are not mutually exclusive and one or more combinations can be used within the scope of the present disclosure to prevent, for example, premature activation of the drug delivery device 10. In a preferred embodiment, the drug delivery device 10 uses one or more mechanical sensors on the body. Other integrated safety mechanisms are described herein with reference to other components of the drug delivery device 10.
II. Feeding and control system
The power and control system 400 includes a power source, which provides the power for various electrical components within the drug delivery device 10, one or more feedback mechanisms, a microcontroller, a circuit card, one or more conductive pads and one or more interconnects. Other components commonly used in such electrical systems may also be included, as will be appreciated by one of skill in the art. The one or more feedback mechanisms may include, for example, audible alarms, such as piezoelectric alarms, and / or light indicators, such as light-emitting diodes (LEDs). The microcontroller can be, for example, a microprocessor. The feed and control system 400 controls various interactions of the device with the patient and interacts with the drive mechanism 100. In one embodiment, the power and control system 400 interacts with the control arm 40 to identify when the sensor 24 in the body and / the trigger mechanism 14 have been activated. The power and control system 400 may also interact with the indicator status 16 of housing 12, which can be a transmitting or translucent material that allows light transfer, to provide visual feedback to the patient. The power and control system 400 interacts with the drive mechanism 100 through one or more interconnections to transmit the status indication to the patient, such as activation, drug delivery, and end of dose. Said status indication can be presented to the patient through audible tones, such as through audible alarms, and / or through visual indicators, such as through LEDs. In a preferred embodiment, the control interfaces between the power and control system and the other components of the drug delivery device 10 are not hooked or connected until activated by the patient. This is a desirable security feature that prevents accidental operation of the drug delivery device 10 and can, in addition, maintain the energy contained in the energy source during storage, transportation, and the like.
The feed and control system 400 may be configured to provide the patient with a number of different status indicators. For example, the power and control system 400 may be configured such that after the sensor has been depressed on the body and / or the trigger mechanism, the power and control system 400 provides a ready-to-start status signal to via status indicator 16 if device startup checks do not provide errors. After providing the ready-to-start status signal and, in one embodiment with the optional body sensor, if the body sensor remains in contact with the patient's body, the power and control system 400 will power the drive mechanism. 100 to begin administration of the drug treatment through the connection of fluid path 300 and sterile fluid line 30. In a preferred embodiment of the present disclosure, the insertion mechanism 200 and the connecting of the fluid path 300 can be directly activated by the actuation by the patient of the activation mechanism 14. During the drug administration process, the system Power and control 400 is configured to provide a dispense status signal through status indicator 16. After the drug has been administered into the patient's body and after the end of any additional residence time, to ensure that substantially all of the dose has been administered to the patient, the feed and control system 400 can provide a status signal ready to remove via status indicator 16. It can be independently verified by the patient with actuation mechanism 100 and drug dose delivery through window 18 of housing 12. Additionally, the feed and control system 400 may be configured to provide one or more alert signals to through the Status Indicator 16, such as, for example, alerts indicative of situations of failure or failure of operation.
Other configurations of the feeding and control system can be used with the drug delivery device of the present disclosure. For example, certain activation delays can be used during drug administration. As mentioned above, one such delay optionally included within the system configuration is a residence time that ensures that substantially all of the drug dose has been delivered before the completion signal is transmitted to the patient. Similarly, activation of drug delivery device 10 may require delayed depression (ie, pushing) of activation mechanism 14 of drug delivery device 10. Additionally, the system may include a feature that allows the patient to respond. to end-of-dose signals and deactivate or turn off the drug delivery device 10. Said feature may similarly require a delayed depression of the activation mechanism to avoid accidental deactivation of the device. Such features provide the drug delivery device with 10 desirable and user-friendly Integration parameters. An additional safety feature can be integrated into the activation mechanism to prevent partial depression and thus partial activation of the drug delivery device. For example, the activation mechanism and / or the power and control system can be configured in such a way that the device is completely off or completely on, to avoid partial activation. These features are described in more detail later in this document with respect to other aspects of the drug delivery device 10.
III. Fluid Path Connector
The present disclosure provides patient-initiated fluid path connectors that provide fluid communication with drug containers and drug delivery devices that utilize fluid path connectors capable of maintaining fluid path sterility before, during and after the operation of the drug delivery device and which enable the security controls for the device to be activated. In one embodiment, a fluid path connector 300 includes a sterile fluid conduit 30, a piercing member 330, a connecting shaft 310, and a sterile sleeve 320, as shown in Figures 2A and 2B. Fluid path connector 300 may optionally further include one or more flow restrictors. Upon proper activation of the drug delivery device 10 by the patient, the fluid path connector 300 is connected to a drug container 50, thereby allowing fluid flow from the drug container (as can force the drive mechanism 100), through fluid path connector 300, fluid line 30, insertion mechanism 200 and into the patient's body. This connection between fluid path connector 300 and drug container 50 may be facilitated by a piercing member 330, such as a needle, which penetrates a pierceable seal 56 (shown in Figures 3A, 3B, 4A and 4B) of the drug container 50. The sterility of this connection can be maintained by making the connection within a flexible sterile sleeve 320. Upon substantially simultaneous activation of insertion mechanism 200, the fluid pathway between drug container 50 and insertion mechanism 200 is complete to allow delivery of the drug into the patient's body.
In at least one embodiment of the present disclosure, piercing member 330 of fluid path connector 300 is caused to penetrate pierceable seal 56 of drug container 50 of drive mechanism 100 by direct action of the patient, such as by depression of the activation mechanism 14 by the patient. For example, the trigger mechanism 14 itself may carry the fluid path connector 300, such that the displacement of the trigger mechanism 14 from its original position also causes the fluid path connector 300 to shift. Preferred embodiment, this connection is activated by the patient by depressing the activation mechanism 14 and thereby actuating piercing member 330 through pierceable seal 56. Because fluid path connector 300 is not connected to drug container 50 until activated by the patient, fluid flow from drug container 50 is prevented until desired by the patient. This provides the patient with an important safety feature, while also maintaining the integrity of the drug container container 50 and the sterility of the fluid path. In such an embodiment, a collapsible or compressible sterile sleeve 320 may be securely affixed between a cap 52 of drug container 50 and connecting shaft 310 of the fluid path connector. Piercing member 330 may reside within sterile sleeve 320 until a connection between fluid path connector 300 and drug container 50 is desired. Sterile sleeve 320 can be sterilized to ensure sterility of piercing member 330 and fluid path prior to device activation and connection between fluid path connector 300 and drug container 50.
As shown in Figure 2A, the fluid path connector 300 can be attached to a drug container 50 and mounted, by various known methods, either fixedly or removably to an assembly platform 20 and / or to housing 12 of drug delivery device 10. The assembly platform may be a separate component of the housing or may be an integrated component of the housing, such as a preformed mounting appearance on the interior surfaces of the housing. In one embodiment, the drug container 50 may be mounted, connected, or otherwise fixed in a fixed position on the mounting platform 20 or housing, while the fluid path connector 300 is mounted, connected, or, otherwise attached to a movable guide 390 which is capable of being moved upon transfer of the trigger mechanism 14 by the patient. In an alternative embodiment, this configuration can be reversed such that the drug container 50 is attached to a movable guide 390 and the fluid path connector 300 is attached in a fixed position on the mounting platform 20 or housing. In either configuration, the sterility of the fluid path is maintained, the fluid flow path is not connected until the patient so desires, and patient-initiated activation causes the drug container and connector to connect. of the fluid path. Although the former configuration is preferred, the latter configuration may be desired in certain embodiments, such as, for example, those using cartridge-type drug containers. Movement by the patient or similar displacement of the activation mechanism 14 causes displacement, either direct or indirect, of the guide 390 to allow a connection between the fluid path connector and the drug container. Said displacement of the guide 390 may optionally be assisted, for example, to reduce the activation force required by the patient acting on the activation mechanism 14, by a series of different deflection members, including springs of compression, extension springs, elastic bands or the like.
Figure 2B shows the fluid path connector 300 and drug container 50 apart from the housing, mounting platform, and other components of drug delivery device 10. As noted above, drug container 50 may include body 58 having a piston seal 60 at one end and a cover 52 at the other end. Fluid path connector 300 may be mounted, connected, or otherwise attached to drug container 50 in cap 52. At least in an initial configuration, a piercing member 330 is maintained within a sterile sleeve 320 with a distal end adjacent or in contact with a pierceable seal of the drug container 50. Piercing member 330 can be a series of cannulas or conduits, such as rigid needles, and can be comprised of a series of materials, such as steel. In at least one embodiment, piercing member 330 is a rigid steel needle. Sterile sleeve 320 is a collapsible or compressible membrane placed between drug container 50 and connecting shaft 310 and provides a sterile environment within which piercing member 330 may reside. Sterile sleeve 320 can be comprised of a number of materials that are compressible or collapsible, but is preferably an elastomeric membrane. The sterile sleeve 320 can have a number of different shapes or configurations, including cones, pyramids, ellipsoids, ovoids, spheres, octahedra (rhombus shaped), and the like, which can be compressed, folded, or otherwise deformed to allow two components Adjacent ones become closer to each other while maintaining the sterility of an interior environment within the cuff. Similarly, sterile sleeve 320 can have one or more aspects, such as longitudinal (i.e., axial) and / or latitudinal (i.e., radial) grooved grooves, ridges, valleys, accordion pleats, and the like, promoting ability to compress or fold. Such aspects may be equidistant or non-equidistant and in a myriad of configurations including along the inner surface, the outer surface, or both surfaces of the sterile sleeve. FIG. 2B shows an embodiment having longitudinal grooves that are equidistant along the outer circumferential surface of the sterile sleeve 320.
Piercing member 330 is maintained in a sterile environment within sterile sleeve 320. This sterile environment is maintained between connecting shaft 310 and cap 52 of drug container 50. Figure 3A shows an exploded view of the arrangement of the fluid path connector components according to at least one embodiment of the present disclosure, while Figure 3B shows an exploded cross-sectional view. These figures include certain components of the drug container, specifically pierceable seal 56 and optional connection bracket 54, as they relate to the connection of the fluid path connector 300. As shown, an interface surface is made to of the sleeve 320A of the sterile sleeve 320 comes into contact with a surface of the sealing interface 56A of the perforable seal 56 during assembly. These corresponding interface surfaces can be retained in position and / or connected by cap 52, as shown in Figures 4A and 4B, so that a distal end of sterile sleeve 320 can be held within cap 52 while that the rest of the sterile sleeve 320 is outside the cap 52. When used, the optional connection bracket 54 can reside within a gap in the gasket 56B of the perforable seal 56 and within the sterile interior environment of the sterile sleeve 320. Alternatively, the perforable seal 56 and the sterile sleeve 320 may be two aspects of a single preformed component (that is, a unified component that has two or more functions). In such a configuration, cap 52 can be similarly used to hold components in place at a proximal end of drug container 50 (and attached to proximal end of body 58). In either of these embodiments, the sterile sleeve 320 may have a container connection opening 320B at a distal end through which piercing member 330 can be translated to pierce pierceable seal 56 and allow fluid flow connection to the drug container 50. Alternatively, the opening in connection 320B can be a closed surface and function as a perforable sealing membrane between the fluid path and the drug container. However, in at least one preferred embodiment of the present disclosure, pierceable seal 56 has a seal body 56C that would be perforated to open the drug container to the fluid path. In an initial position, the distal end of piercing member 330 may reside adjacent to or in contact with seal barrier 56C of pierceable seal 56 to, for example, minimize the travel distance of fluid path connector 300 to pierce the perforable seal 56 and open the drug container to the fluid path. In a particular embodiment, the distal end of piercing member 330 may reside, at least partially, within seal body 56C of pierceable seal 56, but not fully traverse until activation of the device by the patient. When an optional connection bracket 54 is used, for example to ensure axial perforation of pierceable seal 56, piercing member 330 may pass through a gap in piercing member 54A of connection bracket 54.
Sterile sleeve 320 is connected at a proximal end to connection shaft 310. In one embodiment, this connection is facilitated by coupling between shaft connectors 320C of sterile sleeve 320 and corresponding sleeve connectors 310C of connection shaft 310. This coupling can be a press fit, interference fit, thread fit or a series of other connective joints. Drilling member 330 passes through connecting shaft 310 and is held in place in the connecting opening of drilling member 310A. As described below, in one embodiment, the connecting shaft 310 is configured to accept a curved piercing member 330 such that the piercing member passes through and is held in place both in the connecting port of the member Drill 310A as in conduit connection opening 310B. Fluid conduit 30 is connected to the proximal end of piercing member 330 in conduit connecting opening 310B. As a person skilled in the art you will easily appreciate, optionally, a series of glues or adhesives, or other connection methods such as a press fit, an interference fit, a threaded fit, fusion joint, soldering, ultrasonic welding, can be used. and the like to hook one or more of the components described herein. Figures 5A-5C show a connecting shaft 310 according to an embodiment of the present disclosure, with a fluid conduit 30 and a piercing member 330 attached. Figures 5A and 5B show that piercing member 330 can pass through connecting shaft 310. Figure 5C provides a transparent view of connection shaft 310, in an embodiment having a curved piercing member 330 that connects to fluid conduit 30 as described above.
One or more optional flow restrictors can be used within the fluid path connector configurations described herein. . For example, a flow limiter can be used in the connection between piercing member 330 and fluid conduit 30. Drug delivery device 10 is capable of delivering a range of drugs with different viscosities and volumes. Drug delivery device 10 is capable of delivering a drug at a controlled rate (rate) and / or a specified volume. In one embodiment, the drug delivery process is controlled by one or more flow restrictors within the fluid path connector and / or the sterile fluid line. In other embodiments, other flow rates may be provided by varying the geometry of the fluid flow path or delivery line, varying the rate at which a component of the drive mechanism advances within the drug container to dispense the drug therein, or combinations thereof.
In one embodiment of the present disclosure, the connecting shaft itself can be used as part of the fluid path and, optionally, can function as a flow limiter. Figures 6A and 6B show such an embodiment, where the connecting shaft 3310 has a piercing member 3330 and a fluid conduit 3030 connected at opposite ends of an internal opening 3310D of connecting shaft 3310 (visible in view transparent shown in Figure 6C). Accordingly, internal opening 3310D functions as part of the fluid path and can be used to restrict or otherwise modify fluid flow from drug container 50 to insertion mechanism 200 for delivery of drug fluid to the patient's body. For example, internal opening 331OD may have a smaller diameter than fluid conduit 30 to restrict fluid flow through fluid path connector 300. Additionally or alternatively, the internal opening 3310D can be configured to extend the length of the fluid path to extend the time it takes for the drug to flow from the drug container to the patient. For example, although the embodiment shown in FIG. 6C shows a short-distance straight internal opening 3310D, the internal opening may be a tortuous or convoluted path within the connecting axis that extends the fluid path and I or further provides a restriction of additional flow to the system. By using one or more nonreactive materials and / or nonreactive polymers to form connecting shaft 3310, the integrity of the container and the sterility of the fluid path can be maintained.
Referring now to Figures 4A and 4B, upon movement of the trigger mechanism 14 by the patient (in the direction of the solid arrow), the piercing member 330 is caused to penetrate the pierceable seal 56 (through gasket barrier 56C) to open the fluid path from drug container 50 to fluid path connector 300. As described above, because piercing member 330 is maintained in a sterile environment within sterile sleeve 320, sterility of the fluid path is not compromised. The compressible or collapsible sterile sleeve 320 is deformed to allow transfer or displacement of the fluid path connector 300 upon patient initiation. Figure 4A shows an embodiment of the present disclosure using a sterile sleeve 320 and a pierceable seal 56 as separate components, attached to the proximal end of a body 58 of drug container 50 by a cap 52. As described above, without However, 320 the 320 sterile magüito and the perforable seal 56 can be a unified component that provides two or more functions. Also shown is an optional connection bracket 54 that guides piercing member 330 during activation. In this embodiment, the sterile sleeve 320 is shown to deform radially as it compresses in the axial direction. However, in other embodiments, the sterile sleeve 320 may collapse on itself in the axial direction such as in, for example, a sterile accordion-type sleeve 320. By keeping the fluid path disconnected until use by the patient, the sterility of the fluid path and the drug container are maintained. This new configuration also provides an additional patient safety feature that prevents drug flow until desired and is actively initiated by the patient.
As described herein, the fluid path connector, and specifically a sterile sleeve of the fluid path connector, may be connected to the cap and / or pierceable seal of the drug container upon device activation. initiated by the patient. A fluid conduit may be connected at one end to the fluid path connector and at another end to the insertion mechanism such that the fluid path, when opened, connected, or otherwise enabled, travels directly from the drug container, fluid path connector, fluid line, insertion mechanism, and through the cannula for drug delivery into a patient's body. The components that make up the path for fluid flow are now assembled. These components can be sterilized by various known methods and then fixedly or removably mounted on a mounting platform or housing of the drug delivery device 10, as shown in Figure 1B.
Certain optional standard components or variations of the connection of the sterile pathway 300 or drug delivery device 10 are contemplated, while remaining within the scope and scope of the present disclosure. For example, the upper or lower housings may optionally contain one or more transparent or translucent windows 18, as shown in Figure 1A, to allow the patient to view the operation of the drug delivery device 10 or to verify that it has been completed. the drug dose. Furthermore, the drug delivery device 10 may contain an adhesive patch 26 and a patch liner 28 on the underside of housing 12. Adhesive patch 26 can be used to adhere the drug delivery device 10 to the patient's body for delivery of the drug dose. As one skilled in the art would readily understand, adhesive patch 26 may have an adhesive surface for adhesion of drug delivery device 10 to the patient's body. The adhesive surface of the adhesive patch 26 may initially be covered by a non-adhesive patch liner 28, which is removed from the adhesive patch 26 prior to placing the drug delivery device 10 in contact with the patient's body. Removal of the liner from patch 28 can further remove sealing membrane 254 from insertion mechanism 200, opening the insertion mechanism to the patient's body for drug delivery (as shown in Figure 1C). In some embodiments, removal of patch liner 28 can also activate integrated electronics (eg, power supply and control system 400) by supplying them with electricity from an integrated battery. Additionally, as described above, a number of flow limiters can optionally be used to modify the flow of fluid within the fluid path connector.
Similarly, one or more of the fluid path connector components 300 and drug delivery device 10 can be modified while remaining functionally within the scope and scope of the present disclosure. For example, as described above, although the drug delivery device housing 10 is shown as two separate components, the upper housing 12A and the lower housing 12B, these components may be a single, unified component. Similarly, although sterile sleeve 320 is shown as a separate component of pierceable seal 56, it may be a unified component preformed as part of the pierceable seal. As discussed above, a glue, an adhesive, or other known materials or methods may be used to secure one or more components of the fluid path connector and / or drug delivery device to each other. For example, the upper housing and the lower housing may be separate components joined by a glue or adhesive, a threaded fit connection, an interference fit, fusion joint, solder, ultrasonic welding, and the like; or the upper housing and the lower housing can be a single unified component. Such standard components and functional variations would be appreciated by one skilled in the art and are, therefore, within the scope and scope of the present disclosure.
From the above disclosure it will be appreciated that the fluid path connectors and drug delivery devices disclosed herein provide an efficient and user friendly system for automated delivery of drugs from a drug container. The present disclosure provides patient-initiated container connections that maintain fluid path sterility, and drug delivery devices that incorporate such sterile fluid path connectors into drug containers. Such devices are safe and easy to use, and are aesthetically and ergonomically attractive to self-administered patients. The devices described herein incorporate features that make device activation, operation, and lockout easy even for untrained patients. Because the fluid path is disconnected until the patient wishes to administer the drug, the sterility of the fluid path connector, the drug container, the drug fluid, and the device as a whole is maintained. These aspects of the present disclosure provide highly desirable patient storage, transport and safety benefits. Additionally, the new configurations of fluid path connectors and drug devices of the present disclosure maintain sterility of the fluid path through operation of the device. Because the pathway through which the drug fluid travels within the device is completely maintained in a sterile state, only these components need to be sterilized during the manufacturing process. Such components include the drug container of the drive mechanism, the fluid path connector, the sterile fluid line, and the insertion mechanism. In at least one embodiment of the present disclosure, it is not necessary to sterilize the power and control system, the assembly platform, the control arm, the trigger mechanism, the housing, and other components of the drug delivery device. This greatly improves the manufacturing capacity of the device and reduces the associated assembly costs. Accordingly, the devices of the present disclosure do not require terminal sterilization upon completion of assembly. An additional benefit of the present disclosure is that the components described in the present invention are designed so that they are modular so that, for example, the housing and other components of the drug delivery device can be easily configured to accept and drive the shaft connecting shaft 310, connecting shaft 3310, or a number of other variations of the components described herein.
The assembly and / or fabrication of the fluid path connector 300, the drug delivery device 10, or any of the individual components can utilize a number of materials and methodologies known in the art. For example, a number of known cleaning fluids, such as isopropyl alcohol and hexane, can be used to clean components and / or devices. Similarly, a number of known adhesives or glues can be used in the manufacturing process. Additionally, known silicone and / or lubrication fluids and processes can be employed during the manufacture of the new components and devices. Furthermore, known sterilization processes can be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
Fluid path connecting can be assembled in a number of methodologies. In an assembly method, the drug container 50 can be assembled and loaded with a volume of a fluid to administer to the patient. The fluid may be one of the drugs described below, such as a granulocyte colony stimulating factor (GCSF) or a PCSK9-specific antibody (Proprotein Convertase Subtilisin / Kexin type 9), for example. In an assembly method, after loading with a drug, the drug container 50 cannot undergo sterilization (eg, radiation sterilization), so that the drug is not damaged by the high energy rays typically used in the sterilization. Drug container 50 includes a lid 52, a pierceable seal 56, a body 58, and a plunger seal 60. Pierceable seal 56 may be fixedly coupled between cap 52 and body 58, at a distal end of body 58. Body 58 may be loaded with a drug fluid through the open proximal end prior to insertion of the seal of the plunger 60 from the proximal end of the body 58. An optional connection bracket 54 can be mounted on a distal end of the pierceable seal 56. The connection bracket 54 for guiding the Insertion of the piercing member of the fluid path connector into the body 58 of the drug container 50. The drug container 50 can then be mounted on a distal end of the drive housing 130. The sleeve Sterile 320 may be connected to pierceable seal 56 and held in fixed contact by cap 52, as described above. Connecting shaft 310, fluid conduit 30, and piercing member 330 can be assembled together and then connected to the proximal end of sterile sleeve 320 by mating between shaft connectors 320C of sterile sleeve 320 and corresponding sleeve connectors 310C of connecting shaft 310, as shown in Figure 4A. Actuation mechanism 100 may be attached to the distal end of drug container 50. Insertion mechanism 200 can be assembled and attached to the other end of fluid conduit 30. This entire subassembly, including drive mechanism 100, drug container 50, fluid path connector 300, fluid conduit 30, and insertion mechanism 200 can be sterilized, as described above, prior to assembly in drug delivery device 10. Certain components of this subassembly can be mounted on the assembly platform 20 or directly inside the housing 12, while other components are mounted on the guide 390 for activation by the patient.
Manufacture of the drug delivery device 10 may further include the step of attaching both the fluid path connector 300 and the drug container 50, either separately or as a combined component, to the assembly platform 20 or to the housing 12 of the drug delivery device 10. This step can be performed in a sterile or non-sterile environment. It may be possible to carry out this step in a non-sterile environment because the path of the sterile fluid from the drug container 50 to the insertion mechanism 200 may have been previously established. Accordingly, there may be more flexibility in choosing the manufacturing location to install the combined fluid path connector assembly 300, container 50, and insertion mechanism 200 in housing 12 of drug delivery device 10. The manufacturing method further includes attaching drive mechanism 100, container 50, and insertion mechanism 200 to assembly platform 20 or housing 12. Additional components of drug delivery device 10, as described above, including the feed and control system 400, trigger mechanism 14, and control arm 40 can be attached, preformed, or pre-assembled to the platform assembly 20 or to housing 12. An adhesive patch and / or a patch liner may be attached to the surface of the outer housing of the drug delivery device 10 that comes into contact with the patient during operation of the device.
IV. Insertion mechanism
Insertion mechanism 200 includes an insertion mechanism housing 202 having one or more locking windows 202A, a base 252, and a sterile box 250, as shown in Figure 7A. Base 252 can be connected to assembly platform 20 to integrate the insertion mechanism into drug delivery device 10 (as shown in Figure 1B). The connection of the base 252 to the assembly platform 20 can be, for example, such that the bottom of the base is allowed to pass through a hole in the assembly platform to allow direct contact of the base with the body of the patient. In such configurations, the bottom of the base 252 may include a sealing membrane 254 which, in at least one embodiment, is removable prior to use of the drug delivery device 10. Alternatively, the sealing membrane 254 may remain attached to the bottom of the base 252 such that needle 214 pierces the sealing membrane 254 during operation of the drug delivery device 10. As shown in Figures 8A and 8B, the insert mechanism 200 may further include an insert deflection member 210, a shaft 212, a needle 214, a retraction deflection member 216, a clip 218, a guide of the manifold 220, a partition 230, a cannula 234 and a manifold 240. Collector 240 can be connected to sterile fluid conduit 30 to allow fluid flow through collector 240, cannula 234, and into the patient's body during drug administration, as will be described in more detail herein. .
Manifold guide 220 may include an upper chamber 222 and a lower chamber 226 separated by a ring from the manifold guide 228. Upper chamber 222 may include an interface slot of clip 220A for attachable retention of clip 218. Upper chamber 222 may have an internal upper chamber 222A, within which retraction deflection member 216, clip 218, and shaft 212 may reside during an initial blocking stage of operation and an external upper chamber 222B that interacts with insert deflection member 210. In at least one embodiment, insert deflection member 210 and retraction deflection member 216 are springs, preferably compression springs. Shaft 212 may be engageably connected to a proximal end of needle 214 such that axial displacement or translation of shaft 212 causes related movement of needle 214.
As used herein, the needle is understood to refer to various needles, including, but not limited to, conventional hollow needles, such as rigid hollow steel needles and solid core needles, more commonly called trocars. . In a preferred embodiment, the needle is a 27 gauge solid core trocar and, in other embodiments, the needle may be a needle of any size suitable for inserting cannula 234 for the type of drug and drug delivery (eg. , subcutaneous, intramuscular, intradermal, etc.). During assembly, the proximal end of needle 214 is held in fixed contact with shaft 212, while the remainder of needle 214 is allowed to pass through retraction bypass member 216, an opening 218C of clip 218 ( shown in Figure 10A) and the collector guide (220). Needle 214 can further pass through septum 230, cannula 234, manifold 240 through manifold head 242, sterile nozzle 250, and base 252 through opening in base 252A. Collector head 242 may include an internal chamber defined by an inner wall of collector 240. Cannula 234 may be configured in fluid communication with the internal chamber of collector head 242. The septum 230, cannula 234, and manifold 240 may reside within lower chamber 226 of manifold guide 220 and within sterile nozzle 250 until operation of the insertion mechanism. In this position, cannula 234 can reside on a distal portion of needle 214 and be held in place within manifold head 242 of manifold 240 by socket 232. Cap 232 ensures cannula 234 remains substantially fixed and in sealed contact within manifold 240 to, for example, maintain sterility of manifold head 242. Similarly, septum 230 resides substantially fixed and in sealed contact within the top of manifold 240 to maintain sterility of manifold head 242.
Sterile mouthpiece 250 is a collapsible or compressible sterile membrane that is in fixed engagement at a proximal end with manifold 240 and at a distal end with base 252. In at least one embodiment, sterile mouthpiece 250 is held in fixed engagement at a distal end between base 252 and insert mechanism housing 202, as shown in Figures 11A-116C. Base 252 includes an opening in base 252A through which the needle and cannula can pass through during operation of the insertion mechanism, as will be described later. The sterility of the cannula and needle are maintained by their initial position within the sterile portions of the insertion mechanism. Specifically, as described above, needle 214 and cannula 234 are maintained in the sterile environment of manifold head 242 and sterile nozzle 250. Opening of base 252A of base 252 can also be closed from non-sterile environments. , such as, for example, a sealing membrane 254.
Figures 8A-8B, 9 and 10A-10C show the components of the insertion mechanism, according to at least a first embodiment, in greater detail. As shown in Figure 9, the insert mechanism housing 202 may be a substantially cylindrical component having an inner chamber with guide protrusions 204. The protrusions of the guide 204 may be a preformed appearance within the insert mechanism housing 202 or may be a sleeve of the guide protrusion fixedly attached to the proximal inner end of the insert mechanism housing 202. The protrusions of Guide 204 slidably engages manifold guide 220 in through holes 224 in manifold guide ring 228. The insert deflection member 210 initially resides in an excited state between the protrusions of the guide 204 and the inner surface of the insert mechanism housing 202 and between the inner proximal end of the insert mechanism housing 202 and the guide ring of manifold 228 from manifold guide 220. Thus, upon activation by the patient, as further described hereinafter, insert deflection member 210 is caused to abut against collector guide ring 228 of collector guide 220, and exert force on it, as the insert deflection member 210 decompresses and / or deactivates, causing axial displacement in the distal direction of the manifold guide 220 and the components retained within its lower chamber 226. Prior to activation, the insert deflection member 210 is held substantially above the locking windows 202A in a state excited tablet.
In an alternative embodiment of the insertion mechanism shown in Figure 7B, the insertion mechanism 2000 may include two insertion deflection members 2210A, B. The insertion mechanism 2000 further includes the insertion mechanism housing 2202 (shown in view transparent), manifold guide 2220, sterile nozzle 2250, base 2252, and other components similar to those described above with reference to insertion mechanism 200. In the two insert deflection members of the insert mechanism shown in Figure 7B, the manifold guide ring includes two circular platforms on which insert deflection member 2210 A, B can rest. Insert 2000 can function identically to insert mechanism 200, but can provide additional insert force by using multiple insert deflection members 2210 A, B. The components and functions of insertion mechanisms will be further described herein with the understanding that similar or identical components can be used for insertion mechanism 200, insertion mechanism 2000 and all reasonably understood variations thereof.
Figure 10A shows a clip 218, in accordance with an embodiment of the present disclosure. Clip 218 includes opening 218C in platform 218E through which needle 214 and release surfaces 218A and locking surfaces 218B of arms 218D can pass. Clip 218 can be made of any number of elastic materials that are capable of flexing and returning substantially to their original shape. In an original form, clip 218 can flex outward in such a way that ring 218D is not perpendicular to platform 218E. Clip 218 resides within interface slot of manifold guide clip 220A, such that clip 218 is in fixed engagement with manifold guide 220, but arms 218D can flex. In a locked initial stage, the retraction deflection member 216 and shaft 212 (with needle connected 214) are retained between release surfaces 218A and platform 218E of clip 218, and within internal upper chamber 222A of the manifold guide 220 (shown in Figure 9 and Figure 10B). The needle can pass through opening 218C of clip 218 and guide of manifold 220 in septum 230 and manifold 240. The partition 230 resides within the collector 240, as shown in Figure 10C. Collector 240 further includes a collector inlet 240<sup>to</sup>, where the sterile fluid line 30 may be connected. The inlet of the collector 240A can lead to the inner chamber of the collector head 242, such that the connection of the sterile fluid line 30 to the inlet of the collector 240A provides smooth communication between the sterile fluid line 30 and the internal chamber of the collector head 242. Furthermore, the connection between the collector inlet 240A and the sterile fluid line 30 is such that sterility is maintained from the drug container 50 of the drive mechanism 100, through the fluid path connector 300 and the supply line. sterile fluid 30, inside the sterile collector head 242 of the collector 240 and the sterile nozzle 250, to maintain the sterility of the needle 214, the cannula 234 and the fluid pathway to insertion into the patient for drug administration.
The operation of the insertion mechanism is described herein with reference to the above components, in view of Figures 11A-11C. Figure 11A shows a cross-sectional view of the insertion mechanism, according to at least one embodiment of the present disclosure, in a locked and ready-to-use stage. The locking pin (s) 208 are initially located within the locking windows 202A of the insert mechanism housing 202. In this initial position, the collector guide ring 228 of the collector guide 220, the clip 218, and the shaft 212 are retained above the lock windows 202A and the lock pin (s) 208. In this initial configuration , the insert deflection member 210 and the retraction deflection member 216 are each held in their compressed and excited states.
As shown in FIG. 11B, the locking pin (s) 208 (not visible) can be displaced directly by the patient's depression of the trigger mechanism 14. When the patient disables any safety mechanism, such as an optional sensor 24 in the body (shown in Figure 11C), can depress activation mechanism 14 to initiate the drug delivery device. The depression of the activating mechanism 14 can directly cause the control arm 40 to move or move and, directly or indirectly, cause the locking pins 208 to move from their initial position within the locking windows 202A of the housing of the insert 202. The displacement of the locking pin (s) 208 allows insertion bypass member 210 to decompress and / or deactivate from its initial compressed and excited state. Accordingly, the locking pin (s) 208 may function as a second retainer, having: a second retainer retention position (Figure 11A), where the second retainer retains the insert deflection member 210 in the energized state and a second retainer release position (Figure 12B), where the second retainer allows insert deflection member 210 to be deactivated.
As shown in FIG. 11A, the flanges of shaft 212A maintain retraction deflection member 216 in a compressed and excited state between shaft 212 and manifold guide 220 within Internal upper chamber 222A. Shaft 212 is fixedly coupled to the proximal end of needle 214 in recess of shaft 212B. Before operating, the sealing member 254 can be removed from the bottom of the base 252 and the base 252 is brought into contact with the target injection site in the patient's body. As the locking pin (s) 208 are displaced by the trigger mechanism, as described above, and the insert deflection member 210 is allowed to expand axially in the distal direction (i.e., in the direction of the continuous arrow in figure 11 A), the guide of the collector ring 228 is forced by decompression and / or deactivation of the insertion deflection member 210 to translate axially in the distal direction to insert the needle 214 and the cannula 234 into the body of the patient. The axial translation of the collector guide is directed and maintained in rotational alignment by the interaction between the projections of the guide 204 of the housing of the insertion mechanism 202 and the corresponding through holes 224 of the collector guide 220. The release surfaces 218A of the clip 218 engage the shaft 212 and retain the retraction deflection member 216 in a compressed and excited state while the manifold guide 220 moves axially in the distal direction until the clip 218 reaches the end of the projections of guide 204, where clip 218 can be elastically bent outward, as will be described later.
Figure 11B shows a cross-sectional view of a one-stage insertion mechanism with the needle inserted. As shown, the sterile nozzle 250 can collapse as the insert deflection member 210 expands and inserts needle 214 and cannula 234 into the patient's body. During expansion of insertion bypass member 210, manifold 240 moves distally, and because cannula 234 and sterile fluid conduit 30 are fixedly connected to manifold 240, cannula 234, and conduit of sterile fluid 30 also move in the distal direction, as seen in the figures. 11A and 11B. At this stage, as illustrated in FIG. 11B, needle 218 is inserted into the patient's body to place cannula 234 in position for drug delivery. As shown in FIG. 11C, upon insertion of needle 214 and cannula 234 by actuation of insert deflection member 210 as described above, the needle is retracted backward (i.e., it is axially translated into proximal direction) towards the Interior of the insertion mechanism housing 202. The manifold guide 220, the clip 218 and the projections of the guide 204 are dimensioned in such a way that, when the collector 240 moves substantially towards the bottom on the base 252, that is, it reaches its complete axial translation in the distal direction , the clip 218 escapes from the projections of the guide 204 and can be elastically folded out (i.e. in the direction of the hollow arrows shown in Fig. 11B) to disengage the release surfaces 218A from the shaft 212. By disengaging the release surfaces 218A from the shaft 212, the retraction deflection member 216 can expand axially in the proximal direction ( that is, in the direction of the shaded arrow in Figure 11C), from its initial compressed and activated state. Retraction of clip 218 or axial translation in the proximal direction by contact between locking surfaces 218B and the distal ends of guide protrusions 204, as shown in FIG. 11C, is prevented. This locking also prevents axial translation in the proximal direction of the collector guide 220 and the components of the distal insertion mechanism (ie below) of the ring 228 of the collector guide. Thus, clip 218 can function as a third retainer having: a third position-retaining retainer (Figures 11A and 11B), where the third retainer retains retraction deflection member 216 in the excited state; and a third retainer release position (Figure 11C), where the third retainer allows deactivation of the retraction bypass member 216.
The expansion of the retraction deflection member 216 translates the shaft 212 and the needle 214 to which it is connected, axially in the proximal direction. Cap 232 retains cannula 234 inserted into the patient's body through opening in base 252A. Upon retraction of needle 214 from cannula 234, the fluid path is opened from manifold head 242 to the patient's body through cannula 234. As the fluid path connector is made to the drug container and the drive mechanism is activated, the passage of fluid drug treatment from the drug container is forced through the fluid path connector and delivery line. sterile fluid to collector head 242 and through cannula 234 for administration to the patient's body. Accordingly, activation of the insertion mechanism inserts needle 214 and cannula 234 into the patient's body and sequentially retracts needle 214 while maintaining cannula 234 in fluid communication with the patient's body. Retraction of needle 214 also opens the fluid path between collector head 242 and the patient's body through cannula 234. At the end of the drug dose delivery delivery, the cannula 234 can be removed from the patient's body by removing the drug delivery device from contact with the patient.
In some embodiments, cannula 234 is made of a relatively soft flexible material (eg, rubber or plastic), and needle 214 can be constructed of a rigid, relatively hard material (eg, metal). In some embodiments, cannula 234 can be made of a more flexible material than needle 214. The stiffness of needle 214 can facilitate piercing of the patient's skin, and the flexibility of cannula 234 can facilitate patient comfort when cannula 234 is disposed in the patient's body. Accordingly, the combination of needle 214 and cannula 234 can be effective in providing subcutaneous administration of a drug over a period of time (eg, 10 seconds, minutes, hours, or even days) with little or no discomfort to the patient. patient and without impeding the physical activity of the patient.
A method of actuating an insertion mechanism 200 in accordance with an embodiment of the present disclosure includes: removing one or more of the locking pins 208 from one or more corresponding locking windows 202A from the insertion mechanism housing 202, where removal such locking pins 208 allows insert deflection member 210 to expand from its initial excited state; driving, by expanding insert deflection member 210, a manifold guide 220 axially in the distal direction to force exit of needle 214 and cannula 234 at least partially from insert mechanism 200 and entry into the body of the patient; allowing flexing out of clip 218 retained in an upper chamber of manifold guide 220, where clip 210 initially retains shaft 212 and retraction deflection member 216 in an activated state and where flexing decouples one or more surfaces releasing clip 218A from contact with a shaft 212, thereby allowing expansion of retraction deflection member 216 axially in the proximal direction; and retracting needle 214 after retraction of shaft 212 through a fixed connection between needle 214 and shaft 212, while keeping cannula 234 inserted into the patient's body for fluid release.
Certain optional standard components or variations of insertion mechanism 200 or drug delivery device 10 are contemplated, while remaining within the breadth and scope of the present disclosure. For example, the upper or lower housings may optionally contain one or more transparent or translucent windows 18, as shown in Figures 1A-1C, to allow the patient to view the operation of the drug delivery device 10 or verify that the dose drug has ended. Furthermore, the drug delivery device 10 may contain an adhesive patch 26 and a patch liner 28 on the underside of housing 12. Adhesive patch 26 can be used to adhere the drug delivery device 10 to the patient's body for delivery of the drug dose. As one skilled in the art would readily understand, adhesive patch 26 may have an adhesive surface for adhesion of the drug delivery device to the patient's body. The adhesive surface of the adhesive patch 26 may initially be covered by a non-adhesive patch liner 28, which is removed from the adhesive patch 26 prior to placing the drug delivery device 10 in contact with the patient's body. Adhesive patch 26 may optionally include a protective veil that prevents actuation of the optional sensor on body 24 and covers the opening in base 252A. Removal of the coating from patch 28 can remove the protective veil or the protective veil can be removed separately. Removal of the liner from patch 28 can further remove sealing membrane 254 from insertion mechanism 200, opening the insertion mechanism to the patient's body for drug delivery. In some embodiments, removal of patch liner 28 can also activate integrated electronics (eg, power supply and control system 400) by supplying them with electricity from an integrated battery.
Similarly, one or more of the components of insertion mechanism 200 and drug delivery device 10 can be modified while remaining functionally within the scope and scope of the present disclosure. For example, as described above, although the drug delivery device housing 10 is shown as two separate components, the upper housing 12A and the lower housing 12B, these components may be a single, unified component. Similarly, although the protrusions of the guide 204 are shown as a unified preformed component of the insert mechanism housing 202, it may be a separate component fixedly attached to the interior surface of the insert mechanism housing 202. As discussed above, a glue, adhesive, or other known materials or methods can be used to secure one or more components of the insertion mechanism and / or drug delivery device to each other. Alternatively, one or more components of the insertion mechanism and / or drug delivery device may be a unified component. For example, the upper housing and the lower housing may be separate components joined by a glue or adhesive, a threaded fit connection, an interference fit, fusion joint, solder, ultrasonic welding, and the like; or the upper housing and the lower housing can be a single unified component. Such standard components and functional variations would be appreciated by one skilled in the art and are, therefore, within the scope and scope of the present disclosure.
From the above disclosure it will be appreciated that the insertion mechanisms and drug delivery devices disclosed herein provide an efficient and user-friendly system for automated delivery of drugs from a drug container. The new embodiments described in this document provide integrated security features; allow direct activation of the insertion mechanism by the patient; and are configured to maintain sterility of the fluid path. As previously described, built-in safety features include optional body sensors, redundant locks, automatic needle insertion and retraction upon patient activation, and numerous patient feedback options, including visual and auditory feedback options. The new insertion mechanisms of the present disclosure can be activated directly by the patient. For example, in at least one embodiment, the locking pin (s) that hold the insertion mechanism in its locked and energized state move directly from the corresponding locking windows in the insertion mechanism housing by depression of the mechanism by the patient. activation. Alternatively, one or more additional components may be included, such as a spring mechanism, which displaces the locking pin (s) upon direct displacement of the trigger mechanism by the patient without any intermediate steps.
Additionally, the new insertion mechanism configurations and drug delivery devices of the present disclosure maintain sterility of the fluid pathway during device storage, transportation, and operation. Because the pathway through which the drug fluid travels within the device is completely maintained in a sterile state, only these components need to be sterilized during the manufacturing process. Such components include the drug container of the drive mechanism, the fluid path connector, the sterile fluid line, and the insertion mechanism. In at least one embodiment of the present disclosure, it is not necessary to sterilize the power and control system, the assembly platform, the control arm, the trigger mechanism, the housing, and other components of the drug delivery device. This greatly improves the manufacturing capacity of the device and reduces the associated assembly costs. Accordingly, the devices of the present disclosure do not require terminal sterilization upon completion of assembly. A further benefit of the present disclosure is that the components described in the present invention are designed to be modular so that, for example, the housing and other components of the drug delivery device can be easily configured to accept and operate the mechanism insertion mechanism 200, the insertion mechanism 2000 or the connecting shaft 2000 or a series of other variations of the insertion mechanism described herein.
The assembly and / or fabrication of insertion mechanism 200, drug delivery device 10, or any of the individual components can utilize a number of materials and methodologies known in the art. For example, a number of known cleaning fluids, such as isopropyl alcohol, can be used to clean components and / or devices. Similarly, a number of known adhesives or glues can be used in the manufacturing process. Additionally, known siliconization fluids and processes can be employed during the manufacture of the new components and devices. Furthermore, known sterilization processes can be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
The insertion mechanism can be assembled in a series of methodologies. In one method, a shaft is initially connected to a proximal end of a needle. The shaft and needle are inserted into an internal upper chamber of a collector guide, where a retraction deviation member is maintained in an activated state between the collector guide and the shaft. The core, needle, and retraction deflection member are held in this alignment by a clip, where the clip is fixedly and flexibly connected to the manifold guide at a clip interface. A cannula is inserted into a collector and held in place by a socket. A septum is inserted into the manifold at an end opposite the cannula to create a manifold head in between. The manifold, septum, cannula, and socket are inserted into a lower chamber of the manifold guide such that the needle pierces the septum and resides within the cannula. The needle extends beyond the distal end of the cannula to provide a piercing tip. A sterile nozzle is connected to the manifold, where the needle and cannula reside within the sterile nozzle when the sterile nozzle is in an expanded configuration.
An insert spring is inserted into the insert mechanism housing between the housing and one or more guide protrusions extending into the housing from the proximal end. The manifold guide, which has the components attached to it as described herein, is inserted into the insert mechanism housing such that the protrusions on the guide extend through the corresponding through holes in one aspect of the collector guide ring from the collector guide. As the collector guide is moved proximally, the insert deflection member is contacted with the collector guide ring and excited. As the translation of the collector guide and the compression of the insert deflection member reach a point above one or more locking windows of the insert mechanism housing, one or more corresponding locking pins can be inserted to retain the manifold guide in this position and the insert deflection member in the compressed excited state.
The distal end of the sterile nozzle can be positioned and maintained in fixed engagement with the distal end of the insert mechanism housing by coupling the housing with a base. In this position, the sterile nozzle is in an expanded configuration around the needle and cannula and creates an annular volume that may be sterile. A fluid conduit may be connected to the manifold at a manifold inlet such that the fluid path, when open, travels directly from the fluid conduit, through the manifold inlet, to the manifold head, and through of the cannula by retracting the needle. A fluid path connection can be attached to the opposite end of the fluid line. The fluid line connector, and specifically a sterile fluid line connector sleeve, may be connected to a cap and / or pierceable seal of the drug container. The plunger seal and drive mechanism can be connected to the drug container at an end opposite the fluid path connector. A sealing membrane can be attached to the bottom of the base to close the insertion mechanism from the environment. The components that make up the path for fluid flow are now assembled. These components can be sterilized by various known methods and then fixedly or removably mounted on an assembly platform or housing of the drug delivery device.
The manufacture of a drug delivery device 10 includes the step of attaching the base of the insertion mechanism 200 to the assembly platform 20 or housing 12 of the drug delivery device 10. In at least one embodiment, the attachment is such that the base of the insertion mechanism 200 can pass through the assembly platform 20 and / or the housing 12 to come into direct contact with the patient's body. The manufacturing method may further include attaching the fluid path connector 300, the drug container 50, and the drive mechanism 100 to the assembly platform 20 or housing 12. Additional components of the drug delivery device, as described above, including the feed and control system 400, trigger mechanism 14, and control arm 40 may be attached, preformed, or preassembled to assembly platform 20 or to accommodation 12. An adhesive patch and / or a patch liner may be attached to an outer surface of housing 12 that comes into contact with the patient during operation of drug delivery device 10.
One method of actuating the drug delivery device 10 includes the steps of: activation, by a patient, of the activation mechanism 14; displacement of a control arm to actuate an insertion mechanism 200; displacing a guide to translate a fluid path connector 300; and actuating the feed and control system 400 to activate the drive mechanism 100 to drive the flow of fluid drug through the drug delivery device 10, where the Moving the fluid path connector 300 causes piercing member 330 to penetrate pierceable seal 56, thereby opening a fluid path from drug container 50 to fluid path connector 300. The method may further include the step of attaching an optional sensor to the body prior to activating trigger mechanism 14. Additionally, the method of operation may include moving the plunger seal 60 into actuation mechanism 100 to force fluid drug flow through drug container 50, fluid path connector 300, fluid line. sterile 30 and insertion mechanism 200, for administration of the drug to the body of a patient. The method of operation of the drug delivery device 10 can be appreciated by referring to Figures 4A-4B and 11A-11C, as described above.
V. Drive mechanism
Referring to the embodiments shown in Figures 12 and 13, the drive mechanism 100 includes a drive housing 130, an interconnection of the status switch 132 and the drug container 50 having the lid 52, the pierceable seal 56, the body 58 and piston seal 60. Drug container 50 may contain a drug fluid, within the body between the pierceable seal and the plunger seal, for delivery through the insertion mechanism and drug delivery device 10 to the patient's body. The seals described herein can be comprised of a number of materials but, in a preferred embodiment, are comprised of one or more elastomers or rubbers. The drive mechanism may further include a connection bracket 54 to guide insertion of the piercing member of the fluid path connector into the body 58 of the drug container 50. The drive mechanism 100 may further contain one or more members of drive deflection, one or more release mechanisms, and one or more guides, as further described herein. The drive mechanism components operate to force fluid from the drug container to exit through the pierceable seal, or, preferably, through the piercing member of the fluid path connector, for delivery through the fluid connector. the fluid path, the sterile fluid passage and the insertion mechanism in the patient's body.
The drive mechanism may further include one or more contact surfaces located on the corresponding components. Such contact surfaces may be electrical contact surfaces, mechanical contact surfaces, or electromechanical contact surfaces. Such surfaces may initially be in contact and cause decoupling, or initially disconnected and cause coupling, to allow a signal to be sent to and / or from power supply and control system 400. In at least one embodiment, as further described herein, the contact surfaces may be electrical contact surfaces that are initially disconnected and cause them to engage, the contact surfaces may continue via an energy path, or otherwise way, transmit a signal to the power supply and control system 400. In another embodiment of the present disclosure, the contact surfaces are mechanical contact surfaces that are initially in contact and are then decoupled, so that, after said decoupling, said decoupling communicates with the power supply and control system 400. Said signals they can be transferred through one or more interconnects 132 to the supply and control system 400 or, by mechanical action, to the supply and control system 400. Such components can be used in the drive mechanism to measure and send information related to the operating stage of the drive mechanism, which the power and control system 400 converts into tactile, auditory and / or visual feedback to the patient. Such embodiments are described additionally herein. Regardless of the electrical or mechanical nature of the contact surfaces, the movement of the components that enables transmission of a signal to the power control system 400 is enabled by a deflection member 122 that axially translates a contact sleeve 140 into distal direction during device operation.
In a particular embodiment, the drive mechanism 100 employs one or more compression springs as the deflection member or members. Upon activation of the drug delivery device 10 by the patient, the feed and control system can be actuated to directly or indirectly release the compression spring (s) from an activated state . Upon release, the compression spring or springs can rest against and act upon the plunger seal to force fluid drug out of the drug container. The fluid path connection may be connected through the pierceable seal before, simultaneously with, or after activation of the drive mechanism to allow fluid flow from the drug container, through the fluid path connection , the sterile fluid conduit and the insertion mechanism and into the patient's body for drug administration. In at least one embodiment, fluid flows only through a manifold and an insertion mechanism cannula, thereby maintaining sterility of the fluid pathway before and during drug administration. Such components and their functions are described in more detail below in this document.
Referring now to the embodiment of the drive mechanism shown in FIG. 13, the drive mechanism 100 includes a drug container 50 having a lid 52, a pierceable seal 56, a body 58, and a plunger seal 60 and, optionally , a connection bracket 54. Drug container 50 is mounted at a distal end of an actuation housing 130. Compressed within drive housing 120, between drug container 50 and the proximal end of housing 130, there is a drive bypass member 122 and a piston 110, where drive bypass member 122 is configured to rest on a surface. interface 110C of piston 110, as further described herein. Optionally, a cover sleeve 120 can be used between the drive deflection member 122 and the interface surface 110C of the piston 110 to, for example, promote a more even distribution of force from the drive deflection member 122 to the piston 110, prevent buckling of drive deflection member 122 and / or hide the deflection member from the patient's view. The interface surface 110C of piston 110 is made to lie substantially adjacent to or in contact with a proximal end of gasket 60.
Drive mechanism 100 further includes, mounted at a distal end, an interconnect of status switch 132. A contact sleeve 140 is slidably mounted in the drive housing 130 through an axial opening in the housing 130 such that the hooks of the sleeve 140B at a distal end of the contact sleeve 140 are contacted with the piston 110 between the surface of interface 110 and a contact protrusion 110B near the proximal end of piston 140. The piston 110 also includes a locking groove 110A, between the contact protrusion 110B and the proximal end of the piston 110. The contact sleeve 140 has a radially extending ring 140C at its proximal end, on which one or more teeth reside. flexible 140A. An electrical contact 134 may be connected, mounted, printed, or otherwise mounted on ring 140C which, during operation of the drive mechanism, may come into contact with the corresponding interconnect of status switch 132 to complete an electrical circuit or, otherwise, allow transmission to the power and control system to provide feedback to the patient.
The components of the drive mechanism 100, upon activation, can be used to drive the axial displacement in the distal direction of the plunger seal 60 of the drug container 50. Optionally, the drive mechanism 100 may include one or more compliance features that allow for additional axial displacement of the plunger seal 60 to, for example, ensure that substantially all of the drug dose has been delivered to the patient and ensure that the mechanisms contact contacts have connected. For example, in one embodiment of the present disclosure, the hooks of the sleeve 140B are flexing arms that can allow, with the application of sufficient force by the drive deflection member 122 on the piston 110, allowing the interface surface 110C to axially translate past the sleeve hooks 140B to drive additional axial translation of the plunger seal 60 for a compliance push of the drug fluid from the drug container. Additionally or alternatively, the plunger seal 60, itself, may have some compressibility that allows a compliance fluid push of the drug fluid from the drug container.
In at least one embodiment of the present disclosure, the extension of the piston 102 allows a compliance fluid push of the drug from the drug container. In such embodiments, the drive mechanism 100 further includes a piston extension 102 slidably mounted at a distal end and within an axial through hole of piston 110. The extension of the piston 102 can be retained within the piston 110 by the interaction between the extension arms 102B of the piston extension 102 and the connecting grooves 110D of the piston 110, as shown in Figures 14A-14E. The piston extension can be actuated by a piston extension deviation member 106, which is mounted within the axial through hole of piston 110 and initially compressed between piston extension 102 and piston 110. An optional support of the piston deflection member 104 can be used between the piston extension deflection member 106 and the piston extension 102 to, for example, promote a more even distribution of force from the piston deflection member. extension of the piston 106 to the extension of the piston 102. The function of the optional piston extension is described in more detail hereinafter.
The new actuation mechanisms of the present disclosure integrate status indication in the administration of the drug dose. By using one or more status switch interconnects and one or more corresponding electrical contacts, the status of the drive mechanism can be transmitted before, during, and after operation to the power and control system to provide feedback to the patient. Such feedback may be tactile, visual and / or auditory, as described above, and may be redundant such that more than one signal or type of feedback is provided to the patient during use of the device. For example, an initial feedback can be provided to the patient to identify that the system is operational and ready for drug administration. Thereafter, upon activation, the system may provide the patient with one or more indications of the drug delivery status. Upon completion of drug administration, the drive mechanism and drug delivery device 10 can provide an end-of-dose indication. Since the end of dose indication is linked to the piston reaching the end of its axial movement, the actuation mechanism and drug delivery device 10 provide the patient with a true end of dose indication.
In at least one embodiment, as shown in FIG. 12 and FIG. 13, an end-of-dose status indication can be provided to the patient once the status switch 132 has contacted electrical contact 134. at the end of axial movement of piston 110 and plunger 60 into body 58 of drug container 50. In a further embodiment, the incremental status indication conveying various stages of drug administration can be communicated to the patient during operation. In one such embodiment, the hooks of sleeve 140B of cover sleeve 120 may have one or more interconnects that contact one or more electrical contacts on the outer surface of piston 110 during operation. As piston 110 moves axially in the distal direction to push the plunger seal distally, thereby pushing the fluid outlet of the drug container through the end of the pierceable seal, the electrical contacts of piston 110 may sequentially contact interconnecting on the hooks of the sleeve 140B to convey the incremental state of operation. Depending on the number of electrical contacts located on the outer surface of the piston 110, the frequency of the incremental status indication can be varied as desired. The location of the contacts and interconnects can be interchanged or in a number of other configurations that allow completion of an electrical circuit or otherwise allow transmission between components.
In another embodiment of the drive mechanism 500, shown in Figures 15 and 16, the incremental state indication can be measured and transmitted by a different incremental state stem 650 and a corresponding stem interconnect 652. The stem interconnect 652 can be mounted, affixed, printed, or otherwise attached to the stem of the incremental state 650. The stem of the incremental state 650 may be a static component, i.e. does not move or translate, which is mounted at the distal end of contact sleeve 640 and / or at the distal end of drive housing 630, such such that the stem of the incremental state 650 resides within the axial through hole of the contact sleeve 640 and the drive housing 630. The stem of the incremental state 650 further resides within an axial through hole of the piston 610. In such embodiments of the present disclosure, one or more contacts may be located on an internal surface of the piston 610, so that they sequentially interact with one or more corresponding interconnections in the stem of the incremental state 650. As the piston 610 is translated axially in the distal direction to push the plunger seal 60 distally, thereby pushing the fluid outlet from the drug container through the end of the pierceable seal, the contacts of the piston 610 may sequentially contact the interconnect in the incremental state stem 650 to transmit the incremental state of operation. Depending on the number of electrical contacts, the frequency of the incremental status indication can be varied as desired. The location of the contacts and interconnects can be interchanged or in a number of other configurations that allow completion of an electrical circuit or otherwise allow transmission between components.
Figure 17 shows a cross sectional view of the embodiment of the drive mechanism shown in Figure 15 during operation of the drive mechanism. As shown, the incremental state stem 650 may be a static component that is mounted at the distal end of contact sleeve 640 and / or at the distal end of drive housing 630 such that the incremental state stem 650 reside within an axial through hole of the contact sleeve
640 and drive housing 630. As piston 610 translates axially in the distal direction (ie, in the direction of the continuous arrow) to distally push the piston seal 60, the electrical contacts of piston 610 may sequentially contact the interconnection in the stem of the incremental state 650 to transmit the incremental state of the operation through the interconnection of the stem 652. Consequently, the incremental state of the actuation mechanism, and therefore the state of drug administration, can be transmitted to the patient during use of the device.
Referring now to the embodiment shown in Figures 12 and 13, other aspects of the new drive mechanism will be described with reference to Figures 14A-14E. One or more of these aspects can be similarly used in the embodiment shown in Figure 15, or any other variations captured by the embodiments described herein. Figure 14A shows a cross-sectional view of the drive mechanism, according to at least a first embodiment, during its initial locking step. A fluid, such as a drug fluid, may be contained within body 58, between plunger seal 60 and pierceable seal 56, for administration to a patient. Upon activation by the patient, a fluid path connector can be connected to the drug container through pierceable seal 56. As described above, this fluid connection can be facilitated by a piercing member of the fluid path connector that pierces the pierceable seal and completes the fluid path from the drug container, through the fluid path connector. , the fluid line, the insertion mechanism, and the cannula for delivery of the drug fluid to the patient's body. Initially, one or more locking mechanisms (not shown) may reside within the locking slots 110A of the piston 110. Directly or indirectly upon activation of the device by the patient, the locking mechanism may be removed from the locking slots 110A of the piston 110, to allow operation of the drive mechanism. Such a locking mechanism can function as a first retainer having: the holding position of a first retainer, where the first retainer retains the drive deflection member 122 in the activated state; and the first retainer release position, where the first retainer allows actuation bypass member 122 to be deactivated. The first retainer may be structurally and functionally similar to clip 2115 illustrated in Figures 22 and 23A and described in more detail below.
As shown in FIG. 14A, the piston extension bypass member 106 and drive bypass member 122 are both initially in a compressed and excited state. The drive deflection member 122 can be maintained in this state until activation of the device between the internal features of the drive housing 130 and the interface surface 110C of the piston 110. When the locking mechanism is withdrawn from the locking groove 110A of the piston 110, the drive deflection member 122 can expand (ie, unzip) axially in the distal direction (ie, in the direction of the continuous arrow). Such expansion causes actuating deflection member 122 to act on the surface of interface 11C and piston 110 and displace them distally, thereby moving piston 60 distally to push drug fluid out of body 58. The Distal translation of piston 110 causes distal translation of deflection member of piston extension 106 and piston extension 102, when such optional features are incorporated into the device. As shown in FIG. 14B, said distal transfer of piston 110 and piston seal 60 continues to force fluid flow out of body 58 through pierceable seal 56. Premature contact of the state 132 with electrical contact 134 via one or more flexible tips 140A, as shown in Figure 14C. Alternatively, low force springs or other resistance mechanisms may be used in addition to, or alternatively, flexible tips 140A to achieve the same functions. During distal travel of piston 110, hooks on sleeve 140B can slidably contact the outer surface of piston 110. As described above, interconnects and electrical contacts can be placed on these components to provide indication of the incremental state during operation of the drive mechanism.
As the drive mechanism 100 approaches or reaches the end of the dose, the flexible tips 140A may bend outward (i.e. in the direction of the hollow arrows) by the decompression force of the drive deflection member 122. . Such flexing of the flexible tips 140A may allow the interconnect of the state switch 132 to contact the electrical contact 134, completing a circuit or otherwise allowing transmission to the power and control system to provide feedback to the patient. At this stage, one or more administration compliance mechanisms can be used to ensure that the interconnect of the state switch 132 has contacted the electrical contact 134 and / or that substantially the entire drug dose has been administered. For example, in one embodiment of the present disclosure, the hooks of the sleeve 140B are flexing arms that can allow, with the application of sufficient force by the drive deflection member 122 on the piston 110, allowing the interface surface 110C to axially translate past the sleeve hooks 140B to drive additional axial translation of the plunger seal 60 for a compliance push of the drug fluid from the drug container. Additionally or alternatively, the plunger seal 60, itself, may have some compressive capacity that allows a compliant push of the drug fluid from<sup>68</sup> the drug container. For example, when an automatic piston seal, i.e., a piston seal capable of deformation from the initial state, is employed, the piston seal can be caused to deform or jump to provide a fluid compliance thrust of drug from the drug container.
In at least one embodiment of the present disclosure, the extension of the piston 102 allows a compliance fluid push of the drug from the drug container. In such embodiments, the drive mechanism 100 further includes a piston extension 102 slidably mounted at a distal end and within an axial through hole of piston 110. The extension of the piston 102 can be retained within the piston 110 by the interaction between the extension arms 102B of the piston extension 102 and the connection grooves 110D of the piston 110, as shown in Figure 14D. The piston extension can be actuated by a piston extension deviation member 106, which is mounted within the axial through hole of piston 110 and initially compressed between piston extension 102 and piston 110. An optional support of the piston deflection member 104 can be used between the piston extension deflection member 106 and the piston extension 102 to, for example, promote a more even distribution of force from the piston deflection member. extension of piston 106 to extension of piston 102.
As the piston 110 reaches the end of its displacement within the body 58, the extension of the piston 102 can be allowed to move axially in the distal direction by the force exerted by the deviation member of the extension of the piston 106. At this stage, expansion (i.e. decompression) of the piston extension deflection member 106 is allowed in the distal direction so that the extension arms 102B of the piston extension 102 can be moved distally (i.e. in the direction of the continuous arrow) within the connection grooves 110D of the piston 110, as shown in figure 14D As shown in figure 14E, said distal translation (i.e. in the direction of the shaded arrow) of the extension of the piston 102 allows a compliance thrust (shown by dimension C in Figure 14E) of the drug fluid from the drug container. The piston extension 102 can be configured so that the extension arms 102B can contact and apply force on a distal end of the connection grooves 110D to translate the piston 110 distally (i.e. in the direction of the shaded arrow). ). This additional distal transfer of piston 110 can be used to ensure that the interconnect of status switch 132 has contacted contact 134.
As described above, the new actuation mechanisms of the present disclosure integrate status indication into drug dose delivery. By integrating the end-of-dose status indication mechanisms into the axial movement of the piston and therefore into the plunger seal, a true and accurate end-of-dose indication can be provided to the patient. By using one or more contact surfaces on the corresponding components, the state of the drive mechanism can be transmitted before, during and after operation to the power and control system to provide feedback to the patient. Said feedback may be tactile, visual and / or auditory, as described above, and may be redundant, such that more than one signal or type of feedback is provided to the patient during use of the device. Figures 14A-14E show an arrangement that provides the patient with an end-of-dose status indication once the interconnect of status switch 132 has contacted electrical contact 134 at the end of axial displacement of piston 110 and plunger 60 within of the body 58 of the drug container 50. As described above, the new devices described herein can additionally provide an incremental status indication to transmit various stages of drug administration to the patient during operation. In one such embodiment, the hooks of sleeve 140B of cover sleeve 120 may have one or more interconnects that contact one or more electrical contacts on the outer surface of piston 110 during operation. A redundant end-of-dose indication may be used after contact between the sleeve hooks 140B of the contact sleeve 140 and the contact protrusion 110B of the piston 110. The electrical contacts or interconnections along the piston 110 may sequentially contact the corresponding interconnections or contacts on the hooks of the sleeve 140B to transmit the incremental state of operation. Depending on the number of electrical contacts located on the outer surface of the piston 110, the frequency of the incremental status indication can be varied as desired. The location of the contacts and interconnects can be interchanged or in a number of other configurations that allow completion of an electrical circuit or otherwise allow transmission between components.
In another embodiment of the drive mechanism 500, shown in Figures 15-17, the incremental state indication can be measured and transmitted by a separate incremental state stem 650 and a corresponding stem interconnect 652. As shown in FIG. 17, the incremental state stem 650 may be a static component that is mounted at the distal end of contact sleeve 640 and / or at the distal end of drive housing 630 such that the state stem Incremental 650 resides within an axial through hole of contact sleeve 640 and drive housing 630. As the piston 610 is translated axially in the distal direction (i.e., in the direction of the continuous arrow) to distally push the piston seal 60, the electrical contacts of the piston 610 can sequentially contact the interconnect in the state stem incremental 650 to transmit the incremental state of operation through the interconnection of the rod 652. Depending on the number of electrical contacts, the frequency of the incremental status indication can be varied as desired. The location of the contacts and interconnects can be interchanged or in a number of other configurations that allow completion of an electrical circuit or otherwise allow transmission between components. Accordingly, the incremental state of the actuation mechanism, and therefore the state of drug administration, can be transmitted to the patient during use of the device.
In a further embodiment of drive mechanism 500, shown in Figures 18 and 19A-19C, drive mechanism 1000 may be similar to mechanism 100 or mechanism 500 and incorporate the respective components and functions of such embodiments, but use surfaces of mechanical contact instead of electrical contact surfaces, as described above. FIG. 18 shows an isometric view of the drive mechanism 1000 in accordance with a further embodiment of the present disclosure. Figures 19A-19C show cross-sectional views of the actuation mechanism shown in Figure 18 in an initial inactive state, an actuated state, and when the mechanism approaches completion of drug administration, and when the mechanism completes administration. of the drug and triggers an end-of-dose signal. In such embodiments, the interconnect of the status switch is a mechanical trigger 1150 and the contact surface is a plug 1140P. As shown in Figure 19A, the optional piston extension bypass member 1106 and drive bypass member 1122 are both initially in a compressed and excited state. The drive deflection member 1122 can be maintained in this state until activation of the device between the internal features of the drive housing 1130 and the interface surface 1110C of the piston 1110. When the locking mechanism is withdrawn from the locking groove 1110A of the piston 1110, the drive deflection member 1122 can expand (i.e. decompress) axially in the distal direction (i.e. in the direction of the continuous arrow). Such expansion causes the actuating deflection member 1122 to act on the surface of the interface 1110C and the piston 1110 and displace them distally, thereby moving the plunger 1060 distally to push the drug fluid out of the body 1058. The distal translation of the piston 1110 causes the distal translation of the deflection member of the piston extension 1106 and the extension of the piston 1102, when such optional features are incorporated in the device.
As shown in Figure 19B, said distal transfer of the piston 1110 and of the piston seal 1060 continues to force the fluid flow out of the body 1058 through the pierceable seal 1056. As described above, the interconnections and Electrical contacts may be located on these components to provide indication of the incremental state during operation of the drive mechanism. As shown in FIG. 19C, when actuator 1000 reaches the end of the dose, pin 1140P disengages from mechanical trigger 1150 to allow transmission to power and control system 400 to provide feedback to the patient. In one such embodiment, disengagement of pin 1140P from mechanical trigger 1150 allows the trigger to rotate upon being deflected by a deflection member, such as a constant force spring 1170. Initially, the constant force spring 1170 deflects the trigger. 1150 mechanical against 1140P pin. Upon axial translation of the pin 1140P, as described above, the pin 1140P disengages from the mechanical trigger 1150 which is then rotated or otherwise displaced to allow transmission of feedback to the patient. At this stage, one or more delivery compliance mechanisms, as described above, can be used to ensure that pin 1140P has been decoupled from mechanical trigger 1150 and / or that substantially all of the drug dose has been delivered.
The assembly and / or fabrication of the drive mechanism 100, the drug delivery device 10, or any of the individual components can utilize a number of materials and methodologies known in the art. For example, a number of known cleaning fluids, such as isopropyl alcohol and hexane, can be used to clean components and / or devices. Similarly, a number of known adhesives or glues can be used in the manufacturing process. Additionally, known siliconization and / or lubrication fluids and processes can be employed during the manufacture of the new components and devices. Furthermore, known sterilization processes can be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
The drive mechanism can be assembled in a number of methodologies. In an assembly method, the drug container 50 can first be assembled and loaded with a fluid to administer to the patient. Drug container 50 includes a cap 52, a pierceable seal 56, a body 58, and a plunger seal 60. Pierceable seal 56 may be fixedly coupled between cap 52 and body 58, at a distal end of the body 58. Body 58 can be loaded with a drug fluid through the open proximal end prior to insertion of plunger seal 60 from the proximal end of body 58. An optional connection bracket 54 can be mounted on a distal end of pierceable seal 56 Connection bracket 54 to guide insertion of the piercing member of the fluid path connector into body 58 of drug container 50. Drug container 50 can then be mounted at a distal end of drive housing 130.
One or more switching state interconnects 132 may be mounted at a proximal end of drive housing 130. A contact sleeve 140, having one or more sleeve hooks 140B at a distal end and a ring 140C at a proximal end that has an electrical contact 134 thereon, can be mounted to drive housing 130 through an axial through hole from the proximal end of drive housing 130. A drive deflection member 122 can be inserted into a distal end of drive housing 130. Optionally, a sleeve of cover 120 can be inserted into a distal end of drive housing 130 to substantially cover cover deflection member 122. . A piston may be inserted into the distal end of the drive housing 130 and through an axial through hole of the contact sleeve 140, such that a contact protrusion 110B of the piston 110 is proximal to the hooks of the sleeve 140B of the contact sleeve 140 The piston 110 and the drive deflection member 122 and the optional cover sleeve 120 may be compressed within the drive housing 130. Such an assembly places the drive deflection member 122 in an initial compressed and excited state and preferably brings the surface of the piston interface 110C into contact with the proximal surface of the piston seal 60 within the proximal end of body 58. When a piston extension 102 is employed, the piston extension 102 and the piston extension deviation member 106 and the optional piston deviation member holder can be compressed into an axial through hole of the piston 110. The piston, piston deflection member, contact sleeve, and optional components may be compressed and locked in the ready-to-act state within drive housing 130 prior to attachment or mounting of drug container 50.
When one or more interconnects or contacts are used for status indication, such components may be mounted, connected, printed, or otherwise affixed to their corresponding components prior to the assembly of such components in drive mechanism 100. When a separate 650 incremental state stem and a corresponding stem 652 interconnect are used for such an incremental state indication, the stem 652 interconnect may be mounted, affixed, printed, or otherwise affixed to the incremental 650 state stem. The stem of the incremental state 650 and the interconnection of the stem 652 to the proximal end of the contact sleeve 640 and / or the proximal end of the drive housing 630 such that the stem of the incremental state 650 resides within an axial through hole of the contact sleeve 640 and drive housing 630. The incremental condition stem 650 is further mounted to reside within an axial through hole of piston 610.
It will be appreciated that the indicator or end-of-dose interconnects / contact can include any appropriate arrangement, including, for example, mechanical, electrical, electromechanical, ultrasonic, capacitive, or magnetic arrangements. Similarly, the drive mechanism can be of any suitable design.
Alternative arrangements of both the drive mechanism and the indicator or interconnections / end-of-dose contact are illustrated, for example, in Figures 20A-24B. For reasons of clarity, the reference numbers used in Figures 20A-24B are similar to those in the embodiment of Figures 1A-11C, only preceded by the number 2 or 20 "as appropriate to provide a reference number having four digits, i.e. 2XXX. For example, the drug delivery device 10 and the drive mechanism of Figures 20A-24B will be designated by the numbers 2010 and 2100, respectively, as opposed to the drug delivery device 10 and the drive mechanism 100 of the Figures. . 1 A-11C. However, this correlation should not be taken as an indication that the components of Figures 20A-24B with the reference numbers similar to those of the embodiment of Figures 1A-11C are exactly the same as the respective components of Figures 1 A-11C.
As shown in Figures 20A-20C, the drug delivery device 2010 includes a drive mechanism 2100 for receiving a drug container 2050, an insertion mechanism 2200, a fluid path connector 2300 that includes a delivery line. fluid 2030 and a supply and control system 2400, all residing within a 2012 housing, and a 2014 activation mechanism operable by a patient from outside the 2012 housing. The 2012 housing can take any number of configurations and is supplied by numerous components, such as a single-body or multi-component 2012 housing. Certain other components, such as electronics for the power and signaling and activation buttons, and sensors for For safety, they are also omitted for the sake of clarity, but are understood to be standard components within such devices of the drug delivery device 10. Although the 2012 housing, insertion mechanism 2200, fluid path connecting 2300, and supply and control system 2500, as well as activation mechanism 2014 are not discussed in detail, those skilled in the art will appreciate that they can be the same or similar to the components and systems discussed in detail with respect to the other embodiments disclosed herein.
The drive mechanism 2100, the main drug container 050, and a portion of the fluid path connector 2300 are shown isometrically in Figure 21 and exploded in Figure 22. Figures 23A-23C illustrate the mechanism. drive 2100 in cross section as it progresses through various stages of operation. Figures 24A-24B illustrate a lateral cross section of the drive mechanism 2100 in various stages of operation.
The main drug container 2050 contains drug treatment to be injected or infused into the patient and can be a vial or similar container from which a drug treatment can be dosed. To provide a sterile environment for drug treatment, the drug container 2050 may include a cylindrical body 2058 with a pierceable seal 2056 disposed at a distal end and a plunger seal 2060 disposed within a proximal end. Pierceable seal 2056 and plunger seal 2060 can be made of a number of materials, such as one or more elastomeric materials, and are sized and formulated to maintain a seal with body 2058.
The fluid path connector portion 2300 illustrated in the figures includes a piercing bracket 2322, a sterile nozzle 2310, and a piercing assembly 2320. Drill assembly 2320 includes a drill member 2322 that extends from a shaft 2324 that supports drill member 2322 and provides a fluid connection 2326 (see Figure 21) to which fluid conduit 2030 or other fluid connector they can be fluidly coupled to fluidly couple drug container 2050 to insertion mechanism 2200. Connection bracket 2054 is provided adjacent to pierceable seal 2056 and includes an opening adapted to guide insertion of piercing member 2322 of the fluid path connector into pierceable seal 2056 of drug container 2050. Sterile nozzle 2310 is arranged around drill assembly 2320 and provides a sterile environment for completing fluid engagement of fluid path connector 2300. A ring 2052 may be provided to secure a rim of the sterile nozzle 2310, connection bracket 2054, pierceable seal and body 2058 in fixed relation to each other.
Referring to Figures 20A and 20B, in operation, when a patient activates the 2014 trigger mechanism, such as when he presses the illustrated start button, an arm 2015 coupled to the 2014 trigger mechanism exerts an axial force on the drill assembly. 2320 to move piercing member 2322 axially to pierce pierceable seal 2056. Actuator 2100 is adapted for use in cooperation with the proximal end of drug container 2050 to axially advance plunger seal 2060 within body 2058 to dispense drug treatment through fluid path connector 2300. once pierceable seal 2056 has been pierced by piercing member 2322.
The drive mechanism 2100 includes a drive housing 2130 having an axis that matches the A axis of the drive mechanism 2100 (see Figure 21). The axis A may be arranged in coincidence with the axes in the container 2050 and the piston seal 2060. A piston 2110 is at least partially arranged inside the drive housing 2130 for longitudinal movement along the axis of the drive mechanism 2100 . It will be appreciated that the term shaft, when used in connection with drive housing 2130, is not intended to require that the shaft be in a central position of drive housing 2130 or that drive housing 2130 be round.
Piston 2110 is mounted to move between a first retracted position (illustrated in Figure 23A), where piston 2110 is at least partially disposed within drive housing 2130 and a second extended position (illustrated in Figures 23B and 23C), where the piston 2110 extends axially outward from the drive housing 2130. The piston 2110 includes an interface surface 2110C that is arranged to directly face the piston seal 2060 when assembled with a drug container 2050 or to otherwise transmit a driving force to the piston seal 2060. In other words, the piston 2110 of the drive mechanism 2100 of Figures 20A-24B is adapted to exert a dispensing force on the plunger seal 2060 of the drug container 2050 and translate outwardly from a distal end of a housing 2012 to make advance the plunger seal 2060 into the 2050 drug container to dispense the drug. Although the initial position shown in Figure 23A illustrates the interface surface 2110C of piston 2110 arranged substantially adjacent to the distal end of housing 2012, it will be appreciated that, in alternative embodiments, the piston may initially be disposed in a position extending toward outside drive housing 2130. In such an arrangement, at the initial assembly of the drive mechanism 2100 with a drug container 2050, the piston 2110 may initially be at least partially disposed within the proximal end of the drug container 2050.
In order to impart axial movement to piston 2010, drive mechanism 2100 further includes a plurality of piston deflection members 2106, 2122 arranged to move from a first activated position when piston 2110 is in the first position retracted to a second position disabled when piston 2110 is in a second extended position. It will be appreciated that, for the purposes of the present disclosure and the appended claims, the term "deactivated second position" is a relative term. That is, the piston deflection members 2106, 2122 in the "second deactivated position" have less energy than the piston deflection members 2106, 2122 in the "first excited position". This is not to say, however, that the piston bypass members 2106, 2122 in the "second off position" are necessarily completely off or do not store energy.
As long as the piston 2110 is held in the first retracted position, the deflection members 2106, 2122 are kept in their first excited position (see Figure 23A). The piston 2110 is held in the first retracted position by a retaining element or clip 2115. Although any appropriate arrangement can be used to retain the piston 2110 in the first retracted position, clip 2115 can rest against an outer surface of housing 2012 of drug delivery device 10 and be received in a locking slot 2110A of piston 2110. The Figure 23A illustrates clip 2115 arranged in said first retention position. Therefore, those skilled in the art will appreciate that engaging the retaining element or clip 2115 to hold the piston 2110 in its first retracted position with the deflection members 2106, 2122 in its first excited position, allows manipulation of the drive mechanism. 2100 as a self-contained unit such that it can be assembled in the drug delivery device 2010 or in cooperation with a drug container 2050. In operation, however, once clip 2115 is removed or moved to a second release position (see Figures 22B and 23C), piston deflection members 2106, 2122 exert an axial distributional force on the piston. 2110 as they move to a second deactivated position and the piston moves to its second extended position. In at least one embodiment, clip 2115 can be removed by an action caused, directly or indirectly, by movement of trigger mechanism 2014. The removal action of 2115 can be accomplished in various ways. For example, referring to FIG. 22, the action that removes clip 2114 is linear and perpendicular motion relative to axis A of drug container 2050.
In accordance with an aspect of the disclosure as illustrated in the embodiment of Figures 20A-24B, the drive mechanism 2100 has a small size and / or footprint of the device, although capable of providing the necessary dispensing force to push a fluid from drug from a 2050 drug container through a 2030 fluid line for drug delivery through an insertion mechanism 2200. In this embodiment of the drive mechanism 2100, the piston deflection members 2106, 2122 are arranged in parallel, in contrast to the serial arrangement of the embodiments of Figures 1A-11C. Therefore, those skilled in the art will appreciate that the drive mechanism 2100 of Figures 20A-24B provides a significantly smaller footprint than prior art devices or even drive mechanisms 100, 500, 1000 of the other embodiments of the present document.
For the purposes of this disclosure and its claims, when used in connection with deviation members, whether it is a specific embodiment of deviation members, such as springs, or the general use of the term deviation members, the terms parallel should be interpreted. as would those skilled in the art. That is, the terms series, series, or series arranged should be interpreted as arranged and operating springs as they would when connected end-to-end, and the terms parallel, parallel, or parallel arranged should be interpreted as arranged and they work as they would in a side-by-side relationship.
Those of skill in the art will appreciate that for the array members arranged in series, the inverse of the equivalent spring constant will be equal to the sum of the respective inverse of the spring constants of the individual offset members. In contrast, the equivalent spring constant of the deflection members 2106,2122 in a parallel relationship will be the sum of the spring constants of the individual deflection members. Similarly, the dispensing force exerted by the deflection members 2106, 2122 in a parallel relationship will be the sum of the forces exerted by the deflection members 2106, 2122 individually. As a result, the use of deflection members 2106, 2122 arranged in parallel provides the desired dispensing force in a substantially more compact package, allowing the drive mechanism 2100 to be more compact than the embodiments of Figures 1A11C. By extension, the use of the offset members 2106, 2122 arranged in parallel can allow the entire drug delivery device 2010 to be substantially more compact than an arrangement where the offset members are arranged in series.
In this embodiment, deflection members 2106, 2122 are in the form of a pair of concentrically arranged compression springs. In some embodiments, deflection members 2106, 2122 can be wound in opposite directions, thereby balancing the lateral forces created by deflection members 2106,2122. However, alternative provisions are also envisaged. For example, one or more of the deflection members could alternatively, for example, be tension springs, depending on the structure of the drive mechanism components. Furthermore, in the illustrated drive mechanism 2100, the deflection members 2106, 2122 are arranged concentrically with each other and with the piston 2100. However, in an alternative embodiment, the deflection members may alternatively be arranged, as, for example only, in a side-by-side arrangement, or on opposite sides of the piston. In still other embodiments, three or more deflection members could be provided and arranged in parallel in any appropriate configuration. It will further be appreciated that an additional deflection member may be provided and arranged in series with one or more of the deflection members arranged in parallel. For example, in an embodiment where the piston includes an extension, similar to piston extension 102 of the embodiment of Figures 1A11C, for example, an additional deflection member may be provided to engage the piston extension.
Referring now to the embodiment of Figures 20A-24B, the drive mechanism 2100 includes an end of dose indicator 2133. The end of dose indicator 2133 includes a switching interface 2132 and a contact sleeve assembly 2120 adapted to movement with piston 2110. Piston 2110 has an interface surface 2112 that is capable of contacting, or otherwise abutting on, piston seal 2060 to force the drug fluid out of body 2058 through the delivery path connector. 2300 fluid for administration to a patient. In order to provide access of the end of dose indicator 2133 to the interior of drive housing 2130, it includes an access window 2131, the significance of which will be described later.
The contact sleeve assembly 2120 of the embodiment illustrated in Figures 21-23C includes a pair of telescopic sleeves 2124, 2126. The first sleeve 2124 is adapted to move with the piston 2110 as the piston deflection members 2106 , 2122 are disabled. A generally radially extending distal flange 2124A of the first sleeve 2124 is provided underlying the head 2111 of the piston 2110. In this way, one or both deflection members 2106, 2122 abut against flange 2124A, which abuts against piston head 2111 to impart axial movement to piston 2110. Second sleeve 2126 is slidably coupled to first sleeve 2124. the first sleeve 2124 sliding distally out of the second sleeve 2126. In order to allow the second sleeve 2126 to move with the first sleeve 2124 when the first sleeve 2124 extends fully from the second sleeve 2126, a coupling structure is provided. In the illustrated embodiment, sleeves 2124, 2126 include respective flanges 2124B, 2126A that engage when the proximal end of first sleeve 2124 approaches the distal end of second sleeve 2126 (see Figure 23A) to cause the second sleeve 2126 also moves in an axial direction with piston 2110 (see Figure 23C).
However, it will be appreciated that alternative provisions are envisaged. By way of example only, the first sleeve 2124 could alternatively be formed with the piston 2110. In this way, the first sleeve 2124 formed with the piston 2110 will fold out from a second sleeve 2126 in a manner similar to that described above. Furthermore, although the sleeve assembly 2120 has been described as including a pair of telescopic sleeves, an alternative number of sleeves can be used, such as three or more telescopic sleeves. However, the number of sleeves can depend on cooperative structures, such as the relative dimensions of drive housing 2130 and the displacement of piston 2110. For example, in an embodiment using a smaller drive housing, but having a similar piston displacement, three or more telescopic sleeves may be desirable. In some embodiments where multiple sleeves are provided around the deflection members 2106,2122 and the deflection members 2106,2122 are in the form of compression springs, as shown in the illustrated embodiment, the springs in a compressed state and Excited may have a length equal to non-telescopic sleeves 2124, 2126, but have a non-compressed and deactivated length that is equal to the length of telescopic sleeves. Furthermore, although the end of dose indicator 2133 is described in connection with a drive mechanism 2100 that includes a plurality of deviation members arranged in parallel, those skilled in the art will appreciate that the end of dose indicator 2133 could also be used in connection to a drive mechanism including a single deflection device or a plurality of deflection members arranged in series and / or in parallel.
As the sleeve assembly 2120 moves axially outward, the proximal end 2126B of the sleeve assembly 2120 passes the window 2131 of the drive housing 2130. In the particular illustrated embodiment, when the second sleeve 2126 moves axially outward , the proximal end 2126B of the second sleeve 2126 passes the window 2131 of the drive housing 2130.
Switching interconnect 2132 includes a sensor 2134 and an electronic coupling 2136 to the power and control system 2400. At least a portion of sensor 2134 is arranged adjacent window 2131 and is adapted to identify a change in the presence of the sleeve assembly Contact 2120 proximal to window 2131 inside drive housing 2130. For example, in the illustrated embodiment, sensor 2134 can read that sleeve assembly 2120 is no longer present proximal to window 2131.
In order to better illustrate the relationship of the sensor 2134 and the sleeve assembly 2120 during movement of the sleeve assembly 2120, the portions of the sleeve assembly 2120 are separated in Figures 23A-23B; In Figures 24A-24B, housing 2130, sleeve 2126, deflection members 2106, 2122 and end of dose indicator 2133 are shown in cross section taken along line 14-14 of Figure 11. In the illustrated embodiment, the sleeve assembly 1120 is arranged adjacent to the window 2131 when the piston 2110 is in the first retracted position (see Figure 23A) and when the sleeve assembly 1120 begins to fold out with the piston 2110 ( see Figures 23B and 24A). In contrast, the sleeve assembly 1120 is not disposed adjacent to the window 2131 when the piston 2110 is in a second fully extended position (see Figures 23C and 24B). As the proximal end 2126B of the second sleeve 2126 passes through the window, the switch interface 2132 identifies that the sleeve assembly has passed window 2131 and that the end of the dose has arrived and provides that information to the delivery system. and 2400 control. The 2136 electronic coupling can be of any appropriate design. In the illustrated embodiment, for example, sensor 2134 connects directly to a PCB board 2138.
The illustrated switching interface 2132 includes a mechanical sensor 2134 in the form of a pivotally mounted trigger 2135, essentially a mechanical on / off switch. Trigger 2135 is disposed in a first position in contact with sleeve assembly 2120 when piston 2110 is in a first retracted position. As the piston 2110 moves outward from the drive housing 2130, the trigger 2135 slides along the telescopic sleeve assembly 2120 until such time as the proximal end 2126B of the second sleeve 2126 passes through the window 2131, that is, trigger 2135. As second sleeve 2126 passes trigger 2135, trigger 2135 moves to a second position. Movement of trigger 2135 to the second position results in electronic coupling 2135 that provides an end-of-dose signal to the 2400 supply and control system.
However, the switching interconnect 2132 can be of any appropriate design. For example, switching interconnect 2132 may include a sensor of an electromechanical nature, such as that illustrated in Figures 20A-24B, or a sensor of an electrical nature, such as, for example, a reader or optical sensor. Additionally or alternatively, the switching interface 2132 may use an ultrasonic sensor, a capacitive sensor, a magnetic sensor, or a number of other types of sensors. Consequently, the sensor may not require physical contact with the corresponding reference component. In an embodiment that includes an optical sensor, the sensor can read when the presence or absence of the sleeve assembly 2120, for example, read the interior of drive housing 2130 opposite window 2131. The sensor may be configured to, additionally or alternatively, identify at least one of when the sleeve assembly is disposed underlying the window and when the sleeve assembly is not arranged underlying the window, the relative movement of the sleeve assembly with reference to the window or other reference component, the stopping of said movement and the speed or change of movement speed.
Although illustrated as an electromechanical arrangement that reads the position of a telescopic sleeve, any appropriate arrangement can be provided to read the relative position of any appropriate component, with the end of dose indicator providing a signal to the power and control system to indicate that all the drug has been administered. Additionally, the switching interconnects and corresponding contacts and / or reference component can be used to provide incremental status indication in addition to an end of dose indication. For example, in the switching interconnect arrangement described above with reference to Figures 20A-23C, the switching interconnect 2132 may be an electromechanical sensor configured to recognize a series of protrusions, edges or grooves, in the corresponding sleeve 2126 or any another reference component, the contact of which allows the switching interconnect to signal an incremental status indication (eg start of administration, number of volumes administered, duration of piston displacement, etc.) and an end of dose indication. As described herein, a similar incremental status indication can be provided in this configuration using a different type of sensor arrangement. For example, the switch interface 2132 may be an optical sensor configured to recognize a number of markings on the corresponding sleeve 2126 or any other reference component. As the optical sensor recognizes the number of marks, it enables the switch interconnect to signal an incremental status indication (eg, start of delivery, number of volumes delivered, duration of plunger displacement, etc.) and an Indication end of dose. Any appropriate arrangement for reading the relative position of a number of respective marks, edges, grooves, or gauges can be provided on any appropriate reference component, and recognition of such gauges by the switching interconnect enables it to provide a signal to the power system. and monitoring to indicate the incremental state of drug administration, including the final state that all of the drug has been administered. As a person skilled in the art in the relevant techniques will appreciate, the indicators may not necessarily be aspects defined in a reference component and the switching interconnections can be configured to recognize the actual displacement of the reference component itself. In this way, the switching interconnects can be configured to recognize the rate of change, the displacement distance, or other related measurements in the actual displacement of the reference components and allow a signal to the power and control system to provide the patient with such information. or feedback.
Those skilled in the art will appreciate that the embodiments of the present disclosure provide the driving force necessary to push a plunger seal and a drug fluid into a drug container, while reducing or minimizing the drive mechanism and global footprint of the device. Accordingly, the present disclosure provides a drive mechanism that can be used within a more compact drug delivery device. The embodiments of the present disclosure can be similarly used to provide additional strength, as needed for highly viscous drug fluids or for larger volume drug containers.
The embodiments shown and detailed herein disclose only a few possible variations of the present disclosure; Other similar variations are contemplated and incorporated within the scope of the present disclosure.
The drive mechanism may further include one or more contact surfaces located on the corresponding components. Such contact surfaces may be electrical contact surfaces, mechanical contact surfaces, or electromechanical contact surfaces. Said surfaces may initially be in contact and cause their decoupling, or initially disconnected and cause them to engage, to allow a signal to be sent to and / or from the 2400 power control system.
A fluid path connector, and specifically a sterile sleeve of the fluid path connector, may be connected to the cap and / or pierceable seal of the drug container. A fluid conduit may be connected to the other end of the fluid path connector that is itself connected to the insertion mechanism such that the fluid path, when opened, connected, or otherwise enabled, travels directly from the drug container, the fluid path connector, the fluid line, the insertion mechanism, and through the cannula for drug delivery into a patient's body. The components that make up the path for fluid flow are now assembled. These components can be sterilized by various known methods and then fixedly or removably mounted on an assembly platform or housing of the drug delivery device, as shown in Figure 1B.
Certain optional standard components or variations of the drive mechanism 100 or drug delivery device 10 are contemplated, while remaining within the scope and scope of the present disclosure. For example, the upper or lower housings may optionally contain one or more transparent or translucent windows 18, as shown in Figure 1A, to allow the patient to view the operation of the drug delivery device 10 or to verify that it has been completed. the drug dose. Furthermore, the drug delivery device 10 may contain an adhesive patch 26 and a patch liner 28 on the underside of housing 12. Adhesive patch 26 can be used to adhere the drug delivery device 10 to the patient's body for delivery of the drug dose. As one skilled in the art would readily understand, adhesive patch 26 may have an adhesive surface for adhesion of drug delivery device 10 to the patient's body. The adhesive surface of the adhesive patch 26 may initially be covered by a non-adhesive patch liner 28, which is removed from the adhesive patch 26 prior to placing the drug delivery device 10 in contact with the patient's body. Removal of the liner from patch 28 can further remove the sealing membrane 254 from insertion mechanism 200, opening the insertion mechanism to the patient's body for drug delivery (as shown in Figure 1C). In some embodiments, removal of patch liner 28 can also activate integrated electronics (eg, power supply and control system 400) by supplying them with electricity from an integrated battery.
Similarly, one or more of the components of the actuation mechanism 100 and the drug delivery device 10 can be modified while remaining functionally within the breadth and scope of the present disclosure. For example, as described above, although the drug delivery device housing 10 is shown as two separate components, the upper housing 12A and the lower housing 12B, these components may be a single, unified component. Similarly, although electrical contact 134 is shown as a separate component of contact sleeve 140, it can be a unified component printed on the surface of the ring of contact sleeve 140. As discussed above, a glue can be used, adhesive or other known materials or methods for fixing one or more components of the drive mechanism and / or drug delivery device to each other 10. Alternatively, one or more components of the drive mechanism and / or drug delivery device 10 may be a unified component. For example, the upper housing and the lower housing may be separate components joined by a glue or adhesive, a threaded fit connection, an interference fit, fusion joint, solder, ultrasonic welding, and the like; or the upper housing and the lower housing can be a single unified component. Such standard components and functional variations would be appreciated by one skilled in the art and are, therefore, within the scope and scope of the present disclosure.
From the above disclosure it will be appreciated that the drive mechanisms and drug delivery devices disclosed herein provide an efficient and user-friendly system for automated delivery of drugs from a drug container. The new embodiments described herein provide an integrated status indication to provide feedback to the patient. The new driving mechanisms of the present disclosure can be activated directly or indirectly by the patient. For example, in at least one embodiment, the locking pin (s) that hold the drive mechanism in its locked and energized state move directly from the corresponding piston lock slots 110 by depressing the trigger mechanism by the patient. Additionally, the new drive mechanism configurations and drug delivery devices of the present disclosure maintain sterility of the fluid pathway during device storage, transportation, and operation. Because the pathway through which the drug fluid travels within the device is completely maintained in a sterile state, only these components need to be sterilized during the manufacturing process. Such components include the drug container of the drive mechanism, the fluid path connector, the sterile fluid line, and the insertion mechanism. In at least one embodiment of the present disclosure, it is not necessary to sterilize the feeding and control system, the assembly platform, the control arm, the activation mechanism, the housing and other components of the drug delivery device 10. This greatly improves the manufacturing capacity of the device and reduces the associated assembly costs. Accordingly, the devices of the present disclosure do not require terminal sterilization upon completion of assembly. A further benefit of the present disclosure is that the components described in the present invention are designed to be modular so that, for example, the housing and other components of the drug delivery device can be easily configured to accept and operate the mechanism drive 100, drive mechanism 500 or connecting shaft 2000 or a number of other variations of the drive mechanism described herein.
Manufacture of a drug delivery device 10 includes the step of attaching both the drive mechanism and the drug container, either separately or as a combined component, to a platform or assembly housing of the drug delivery device. The manufacturing method further includes attaching the fluid path connector, drug container, and insertion mechanism to the mounting platform or housing. Additional components of the drug delivery device, as described above, including the feed and control system, trigger mechanism, and control arm, can be attached, pre-formed, or pre-assembled to the platform or assembly housing. An adhesive patch and patch liner can be attached to the housing surface of the drug delivery device 10 that contacts the patient during operation of the device.
SAW. Cartridge refill-finish
The sterile fluid pathway assemblies described above can be loaded with pharmaceutical treatments, such as the drugs described below, using standard loading equipment and systems. This advantage is enabled by the loading-finishing cartridges described below that function to maintain the sterility of fluid path assemblies and allow removable nesting, mounting, or otherwise inserting into trays for standard loading processes. finish as discussed further below. The actuation mechanisms, fluid path connectors, insertion mechanisms, and other components and subcomponents of drug delivery devices described below in relation to Figures 25-47 can be implemented in any of the delivery devices. of drugs described above in relation to Figures 1A-24B. Furthermore, any of the manufacturing methods and methods of use described below can be applied to the drug delivery devices described above in connection with Figures 1A-24B.
Turning to FIG. 25, a schematic representation of an example of a drug delivery device 10 illustrating aspects of the disclosure is illustrated. Device 10 includes housing 612 having an activation mechanism 614. For ease of understanding, housing 612 is shown schematically. Based on the disclosure, the device further includes a 616 charge-finish cartridge. The refill-fill cartridge 616 includes a drug container 618, a fluid path assembly 620 that includes a fluid path connector 622, and a needle insertion mechanism 624. The fluid path assembly 620 it may include an additional structure that facilitates the arrangement of various components, including, for example, a fluid conduit 26. Fluid path connector 622 is disposed substantially adjacent to a distal end 628 of drug container 618 and needle insertion mechanism 624 is disposed substantially adjacent to a distal end 630 of fluid path connector 622. In In the illustrated embodiment, the drug container 618 is generally horizontal and perpendicular from a vertically positioned needle insertion mechanism 624. However, it will be appreciated that the components may be located in any appropriate manner.
Administration of a drug contained in drug container 618 can be initiated by activation mechanism 614. Activation mechanism 614 may include, for example, activation mechanisms manually operated by a patient or automatically activated by, for example , a power and control module 632 which may include, by way of further example, a microprocessor or other automatic management arrangement with appropriate connections. In this embodiment, the activation mechanism 614 is a button 634 that can be arranged, for example, along an external surface of the housing 612 and can be selectively depressed by the patient. It will be appreciated that the drug delivery device 10, as well as the activation mechanism 614, can be of any appropriate design.
The power and control module 632, if included, may include a power source, which provides the power for various electrical components within the drug delivery device, one or more feedback mechanisms, a microcontroller, a circuit card, one or more conductive pads and one or more interconnects. Other components commonly used in such electrical systems may also be included, as will be appreciated by one of skill in the art. The one or more feedback mechanisms may include, for example, audible alarms, such as piezoelectric alarms, and / or light indicators, such as light-emitting diodes (LEDs). The microcontroller can be, for example, a microprocessor. The power and control module 632 controls various interactions of the device with the patient and can interact with one or more components of the drug delivery device 10. In one embodiment, the power and control module 632 can identify when a sensor is on the body. and / or the activation mechanism 614 have been activated. The power and control module 632 can also interact with a status indicator, which can be a transparent or translucent material that allows light transfer, to provide visual feedback to the patient. The supply and control module 632 can interact with a drive mechanism and / or the integrated sterile fluid path connector and drug container 618 through one or more interconnections to transmit the status indication to the patient, such as activation, drug administration and / or end of dose. Said status indication can be presented to the patient through tactile feedback, such as vibration; Audible tones, such as through audible alarms, and / or through visual indicators, such as through LEDs. In a preferred embodiment, the control interfaces between the power and control system and the other components of the drug delivery device are not hooked or connected until activated by the patient. This is a desirable security feature that prevents accidental operation of the drug delivery device and can also keep stored energy in the energy source during storage, transportation, and the like.
The power and control module 632 can be configured to provide the patient with a number of different status indicators. For example, the power and control module 632 may be configured such that after the sensor is pressed into the body and / or the trigger mechanism, the power and control module 632 provides a ready-to-start status signal to via status indicator 16 if device startup checks do not provide errors. After providing the ready-to-start status signal and, in one embodiment with the optional body-mounted sensor, if the body-mounted sensor remains in contact with the patient's body, the power and control module 632 will actuate the drive mechanism. to begin drug treatment delivery through the 622 integrated sterile fluid path connector and 26 sterile fluid conduit. In a preferred embodiment of the present disclosure, insertion mechanism 624 and actuation mechanism can be directly activated by patient actuation of activation mechanism 614. The integrated sterile fluid path connector is connected (i.e. the fluid path is open) by the pneumatic force of the drug fluid within drug container 618 created by activation of the drive mechanism, as detailed below in the present document. During the drug delivery process, the feed and control module 632 is configured to provide a dispensing status signal through the status indicator. After the drug has been delivered to the patient's body and after the end of any additional residence time, to ensure that substantially all of the dose has been delivered to the patient, the 632 Power and Control Module can provide a status signal ready to remove via status indicator. The patient can independently verify this by viewing the drive mechanism and drug dose delivery within the drug container through a window in housing 612. Additionally, the feed and control module 632 can be configured to provide one or more signal signals. Alerts via the status indicator, such as alerts indicative of failures or malfunction situations.
Other configurations of the feeding and control system can be used with the new drug delivery devices of the present disclosure. For example, certain activation delays can be used during drug administration. As mentioned above, one such delay optionally included within the system configuration is a residence time that ensures that substantially all of the drug dose has been delivered before the completion signal is transmitted to the patient. Similarly, activation of the device may require a prolonged depression (i.e., push) of the activation mechanism 614 of the drug delivery device 10 prior to activation of the drug delivery device. Additionally, the system may include a feature that allows the patient to respond to end-of-dose signals and disable or turn off the drug delivery device. Such a feature may similarly require a delayed depression of the activation mechanism, to prevent accidental deactivation of the device. These features provide desirable parameters of security integration and ease of use to drug delivery devices. An additional safety feature may be integrated into the activation mechanism to prevent partial depression and therefore partial activation of drug delivery devices. For example, the activation mechanism and / or the power and control system can be configured in such a way that the device is completely off or completely on, to avoid partial activation. Such features are described in more detail hereinafter with respect to other aspects of the novel drug delivery devices.
When included, the power and control module 632 can include a processor (not shown) and a memory component (not shown). The processor may be microprocessors or other processors as known in the art. In some embodiments, the processor may be made up of multiple processors. The processor may execute instructions to generate the delivery signal and control the delivery of a drug contained in drug container 618. Such instructions may be read or incorporated in a computer-readable medium, such as the memory component, or provided external to the processor. In alternative embodiments, hard-wired circuitry can be used in place of, or in combination with, software instructions to implement drug delivery. Therefore, the embodiments are not limited to any specific combination of hardware and software circuitry.
The term "computer readable medium," as used herein, refers to any medium or combination of media that participates in providing instructions to the processor for its execution. Such a medium can take many forms. The memory component can include any form of computer-readable medium, as described above. The memory component can include multiple memory components.
The 632 power and control module can be included in a single housing. In alternative embodiments, the power and control module 632 can include a plurality of components operatively connected and enclosed in a plurality of housings.
The power and control module 632 can be configured to generate a delivery signal based on the patient drive, preprogrammed drive, or remote drive. The feed and control module 632 may be coupled in communication with the refill-fill cartridge 616 and / or the drug container 618, the fluid path connector 622 and / or the needle insertion mechanism 624 individually.
In accordance with one aspect of the embodiments of the disclosure, in the illustrated embodiment, actuation of the trigger mechanism 614 herein, depression of button 634 results in coupling of fluid path connector 622, such as will be described in greater detail below. This same action on the part of the patient can activate the needle insertion mechanism 624 to inject a needle or cannula into the patient, as will also be explained in greater detail below. Therefore, activation mechanism 614 results in the termination of a drug path from drug container 618 through fluid path connector 622, fluid line 26, and needle insertion mechanism 624. to the patient (not shown). Actuation of the activation mechanism 614 can also result in an actuation mechanism that acts on the structure associated with the drug container 618 to force the fluid through the sterile pathway. In one embodiment of the present disclosure, the needle insertion mechanism 624 can be activated to retract the patient's needle, giving a clear indication of the end of dose administration upon completion of drug administration. Housing 612 may additionally include, for example, a window through which drug container 618 can be viewed to confirm drug administration.
In accordance with one aspect of the embodiments of the disclosure, the finish-fill cartridge 616 is constructed and loaded prior to assembly in housing 612 of the drug delivery device 10. In this regard, the finish-fill cartridge 616 it is strong enough to withstand procedures to sterilize the charge-finish cartridge 616, in some embodiments before loading and, in some embodiments, after loading. After sterile construction and loading of the 616 finished refill cartridges, the device can be placed as needed within a drug delivery device 10. In either case, the sterility of the fluid path 620 assembly and the container of the Drug 618 are maintained through aspects of the assembly, loading and manufacturing processes. The final assembly of the drug delivery device 10 can thus be performed outside of a sterile environment. Because they only need to be sterilized, and have been sterilized, the components of the sterile fluid path assembly 620 and the remainder of the drug delivery device 10 do not need sterilization (ie, terminal sterilization). This provides a number of advantages. New embodiments of the present disclosure may also alleviate the need to charge the drug delivery device at the time of use, although some embodiments of the present disclosure may also be used in devices configured for charging at the time of use.
In accordance with another aspect of the embodiments of the disclosure, various Individual component embodiments of the charge-finish cartridge 616 may be assembled in various configurations to provide various embodiments of the charge-finish cartridge 616. The following disclosures describe exemplary structures of individual elements that can be incorporated into the refill-finish cartridge 616 and are incorporated herein by reference for all that is disclosed therein:
United States Application Serial No. 13 / 600,114 filed on August 30, 2012; United States Application Serial No. 13 / 599,727 filed on August 30, 2012; United States Application Serial No. 13 / 612,203 filed on September 12, 2012; and 13 / 796,156 filed on March 12, 2013. Fig. 26B is a diagram of examples of variables for possible connection structures between individual components that can give various configurations of embodiments of charge-finish cartridges 616, although Figure 26A show an example of a charge-finish cartridge 616 that identifies the aspects referenced in figure 26A. For ease of understanding, the same reference numbers are used as in Figure 25. The individual components as well as the interactions and connections between the individual components can have various designs. For example, the needle insertion mechanism 624 can be of any suitable design. Similarly, container 618 and fluid path connector 622 can each be of any appropriate design.
Similarly, interactions between components can be of any appropriate design. For example, the coupling of the fluid path connector 622 with the drug container 618 may include a threaded or snap connection, an interference fit or an external bracket or other arrangement, provided that a tight seal is obtained. Similarly, the coupling of the fluid path connector 622 with the needle insertion mechanism 624 may include a threaded or snap connection, an interference fit, a tongue and groove arrangement, an external bracket, or some other arrangement including, but not limited to, the use of a fluid line between fluid line connector 622 and needle insertion mechanism 624 for connection. Furthermore, in some embodiments, the coupling of the fluid path connector 622 with the needle insertion mechanism 624 may be decoupled after the charge-finish process in order to allow the needle insertion mechanism 624 to be oriented such that it is not axially with the rest of the 616 finish-fill cartridge, provided the sterile fluid connection is maintained.
In various embodiments, the charge-finish cartridge 616 may be maintained with the components in axial alignment during the charge-finish process, as well as in use with a drug delivery device 10. This is, for example, the insertion mechanism. Needle 624 may be axially disposed with the remainder of the finished refill cartridge 616 during the refill-finish process, as shown in Figure 26B, and in use in a drug delivery. In other embodiments, the finish-fill cartridge 616 may be kept with the components in axial alignment during the finish-fill process, as illustrated in Figure 26B, while the components may be kept in a different alignment than axial in use with a drug delivery device 10. For example, as illustrated in FIG. 25, the needle insertion mechanism 624 is arranged separate from the fluid path connector 622 and the drug container 618 and at a 90 ° orientation. In other embodiments, the charge-finish cartridge 616 may be held with the components in a non-axial alignment during both the charge-finish process, albeit axially aligned during use with a drug delivery device 10. In other embodiments, the charge-finish cartridge 616 can be held with the components in a non-axial alignment during both the charge-finish process and in use with a drug delivery device 10.
Furthermore, although not included in all embodiments, in order to provide added structural integrity to the finish-fill cartridge 616, a vehicle may be provided, as will be explained in more detail below. Said vehicle may be integrated with the structure of the charge-finish cartridge 616 in such a way that it is kept around or along at least a portion of the charge-finish cartridge 616 in the drug delivery device 10, or said vehicle can be completely or partially disposable. A vehicle can perform a number of functions, such as maintaining the relative positions of several of the finished charge cartridge components during assembly, a charge-finish process, or other operations performed on the charge-finish cartridge with a device. of drug delivery 10, such as, attaching the refill-fill cartridge 616 to a drug delivery device 10 or in connection with the operation of a drug delivery device 10. More detailed explanations of various examples of such structures in various configurations are set forth below; it is not intended to limit structures to those particular configurations. Rather, the individual arrangements explained are provided as examples of various possible configurations and structures within the scope of this disclosure.
Figure 27 shows an exploded view of one embodiment of the charge-finish cartridge 716 of the present disclosure. For ease of understanding, the number used in Figure 25 is used in other examples of embodiments of the disclosure with numerical prefixes; In this embodiment, 1XX will be used. The refill-fill cartridge 716 of this embodiment includes a fluid path assembly 720 connected to a drug container 718.
Fluid path assembly 720 includes a needle insertion mechanism 724 coupled to a fluid path connector 722 by a fluid passage 726. A proximal end of needle insertion mechanism 724 is connected to one end distal of a fluid line 726, which is connected at its proximal end to the fluid line connector 722.
The needle insertion mechanism 724 can be of any appropriate design as long as it can be sterilized prior to placement of the refill-cartridge 716 in a drug delivery device. Examples of such 724 needle insertion mechanisms for implants and liquid drugs and disclosed in United States Application Serial No. 13 / 599,727 filed August 30, 2012, are incorporated herein by reference for all. what is disclosed in it. It will be appreciated that the needle insertion mechanism 724 of FIG. 27 includes an axial structure such that the delivery needle (not visible in FIG. 27) extends axially from a distal end of the charge-finish cartridge 716 to the administration. However, it will be appreciated that, alternatively, a needle insertion mechanism 724 could be used that is arranged at an angle to an axis of the fluid path 722 and / or drug container 718 connection.
The components of the fluid line assembly 720, including the needle insertion mechanism 724, the fluid line connection 722 and the fluid line 726 are made of materials that can be sterilized by conventional sterilization techniques and machinery. Fluid line 726 can be formed of any appropriate material, for example, a length of flexible tube, such as a plastic tube. It will be appreciated, however, that the fluid path connection 722 and the needle insertion mechanism 724 may be directly attached in some embodiments (not illustrated in Figures 27 and 28).
The components of the fluid path assembly 720 can be sterilized prior to such connections or can be connected prior to sterilization as a unified component. If sterilized prior to such connections, the fluid path assembly 720 may include an additional gasket at the fluid path connection 722, such as a permeable seal that can be drilled during assembly or actuation (not illustrated).
The drug container 718 of this and each of the embodiments may be of any appropriate material and of any appropriate shape and size, and may include a gasket to maintain the integrity and sterility of a drug contained therein. For example, the drug container 718 may be made of glass, plastic, or other suitable material. The drug container 718 of this and each of the embodiments may include a structure that facilitates handling, mounting within a drug delivery device, sterilization, and / or interface with other components of the finished charge cartridge 716. For example, a tab can be provided at any appropriate location along the drug container 716. Said flange 719 can be integrally formed with the drug container 718 or it can be a separate element that is fixed to the drug container. In the illustrated embodiment, tab 719 is a separate component that is attached to a proximal end of drug container 718.
It will be appreciated that any appropriate drive mechanism can be provided to move the drug from the drug container 718 to the fluid path assembly 720 in embodiments of the disclosure. For example, US application Serial No. 13 / 600,114, filed August 30, 2013, discloses an embodiment of an actuation mechanism associated with a drug container, and is incorporated herein by reference. for everything disclosed in said request.
In order to facilitate both loading of the drug container 718 and administration of medication from the drug delivery container, the drug container 718 may include openings 718a, 718b at the proximal and distal ends 6127, 728, respectively. In order to seal the drug container 718, a permeable seal 150 may be provided at a distal end 728 of the drug container 718. In this way, once loaded, a drug contained within drug container 718 can be maintained in a sterile environment until such time as gasket 150 is pierced through fluid path connector 722 to complete the fluid path. Leaky seal 150 can be of any suitable design and material.
The distal end 728 of drug container 718 can be assembled with fluid path assembly 720 for sterilization before or after loading, as will be explained in greater detail below. FIG. 28 shows an enlarged cross-sectional view of the fluid path connector 722 and the leaky seal 150 of FIG. 28, after these components have been assembled and are ready for sterilization. Although leaky seal 150 may be a single thin membrane 762 or the like through opening 718b at the distal end 728 of drug container 718, leaky seal 150 may include an additional structure that facilitates connection to drug container 718. and / or the fluid path connector 722. As shown, in at least one embodiment of the present disclosure, the leaky seal 150 is in the form of a container tip that covers the drug container 718, in addition to providing support for the fluid path connector 722. In this In one embodiment, the permeable seal 150 may include a portion 152 that rests within the drug container 718, providing a mating surface for mounting the permeable seal 150 to the drug container 718. To help maintain the connection of gasket 150 with drug container 718, a cap 151 can be provided around the portions of leaky gasket 150 and drug container 718, such as around an edge in drug container 718. Said cover 151 may be of any appropriate material, such as aluminum foil. Although drug container 718 contacts permeable seal 150, it will be appreciated that alternative designs can also be provided.
Leaky seal 150 may also have an extension 153 that facilitates mounting with the fluid path connector 722. In the embodiment shown in Figure 28, the fluid path connector 722 includes a shaft 154 through which it can cannula 158 be extended. Those skilled in the art will appreciate that, as used herein, the term cannula 158 includes a needle or cannula that can be operative to provide the required fluid connection. .Fluid line 726 is fluidly connected to cannula 158 when it extends from a surface of shaft 154. Shaft 154 of fluid path connector 722 can be used, as shown herein, to mount, securing or otherwise connecting to extension 153 of permeable joint 150, the proximal end of cannula 158 being disposed within a hole 760 of extension 153. Before completing a fluid path between drug container 718 and fluid line 726, cannula 158 is held in position as illustrated in FIG. 28.
Leaky seal 150 has a portion that acts as a membrane 762 that can be pierced by cannula 158. In the embodiment of Figures 27 and 28, membrane 762 is generally arranged perpendicular to cannula 158 to close drug container 718 from fluid path connector 722, thereby blocking the fluid path from drug container 718 to fluid line 726. Upon activation by the patient, a portion of the leaky seal 150 that blocks the drug container 718, herein the membrane 762, is caused to be pierced by the cannula 158 of the fluid path connector 722, completing thus the fluid path and allowing the drug fluid to pass from container 718 to cannula 158 and fluid conduit 726 and needle insertion mechanism 724. To facilitate perforation, extension 153 of permeable seal 150 may be tilted out in response to sufficient axial pressure, for example, to allow cannula 158 to pierce membrane 762 to complete the fluid path.
In accordance with another aspect of the embodiments of the disclosure, the drug container 718, the fluid path connector 722, and the needle insertion mechanism 724 of the charge-refill cartridge 716 have sufficient structural integrity to be used in a charge-finish process and its assembly in a housing of a drug delivery device. It will be appreciated that any appropriate fluid path connector 722 can be incorporated into embodiments of the disclosure. For example, a mounted fluid path connector can be used, as disclosed in, for example, U.S. Serial Application No. 13 / 612,203 filed on September 12, 2012. Also, an integrated fluid path connector can be used, as disclosed in, for example, US Serial Application No. 13 / 796,156 filed on September 12, 2013. Each of these applications is incorporated herein by reference.
Similarly, it will be appreciated that any appropriate connection can be provided between the fluid path connector 722 and the needle insertion mechanism 724. While examples of some connections are disclosed in detail, it is not the applicant's intention to limit the divulgation. Such a connection may include, for example, a snap connection (see Figures 45-47), a threaded connection (see Figures 40-44), an interference connection, a tongue and groove connection, an external bracket (see Figure 27), or other appropriate connection.
Turning to FIG. 27, in order to provide additional structural integrity to said interface between the fluid path connector 722 and the leaky seal 150 and / or between the fluid path connector 722 and the fluid insertion mechanism. needle 724, a vehicle 742 can be provided. Vehicle 742 of this embodiment includes a connecting collar 740 and a body 6141. For manufacturing purposes, the connecting collar 740 may itself include multiple components, as illustrated in FIG. 27, that can be fitted around the fluid path connector 722, the leaky seal 150, and a portion of the drug container 718 by any appropriate mechanism. It will be appreciated, however, that alternatively a unitary connecting collar 740 could be provided. It will be further appreciated that connection collar 740 may not be necessary or desirable in all embodiments and that connection collar 740 may be provided as an integrated part of the design or may be fully or partially disposable during assembly or sterilization processes.
Body 6141 can provide additional structural integrity that can support fluid path assembly 720 during sterilization and assembly processes. Although any appropriate coupling can be provided, connection collar 740 can facilitate coupling of body 6141 around fluid path assembly 720. In the illustrated embodiment, the connection collar 740 includes a pair of protrusions 744 (only one being visible in Figure 27) that mate with a pair of recesses 746 in the body 6141. As with connection collar 740, it will further be appreciated that body 6141 may not be necessary or desirable in all embodiments, and that such body 6141 may be provided as an integrated part of the design or may be wholly or partially disposable during assembly or sterilization processes. In order to allow the needle insertion mechanism 724 to function to deliver the medication, the body 6141 may include an opening 6 741a through which a delivery needle may extend during use.
For operational operation, the needle insertion mechanism 724 may be coupled to the fluid path connector 722, and the fluid path connector 722 may be connected to leaky seal 150 with the needle insertion mechanism 724. maintained in the non-piercing configuration through the sterilization, loading and assembly processes. In this way, the finish-fill cartridge 716 may appear as shown in FIG. 29, the fluid path assembly 720 residing entirely hidden from the external environment by vehicle 742. Once the drug container 718 is loaded with a pharmaceutical treatment, a gasket 764 can be provided at the proximal end 6127 of the drug container 718 to provide a closed fill-cartridge 716 that can be inserted into a drug delivery device. suitable drug. In the embodiment illustrated in Figures 29-30, an elastomeric plunger seal 764 is inserted into the proximal end 6127 of drug container 718. It will be appreciated, however, that another suitable sealing arrangement can be provided. In Figures 29 and 30, the arrangement of the fluid path connector 722, the container 718 and the insertion mechanism 724 relative to each other can be considered to be a first configuration. The first configuration can facilitate the manufacturing process, for example by allowing the use of standard loading equipment and systems. Although the first configuration shown in Figures 29 and 30 involves axial alignment of container 718 and insertion mechanism 724, in other embodiments, the first configuration may involve non-axial alignment of container 718 and insertion mechanism 724, or any another relative placement of container 718 and insertion mechanism 724. Subsequently, when assembled into the drug delivery device 610, as illustrated in FIG. 25, the fluid path connector 722, container 718, and insertion mechanism 724 may be arranged relative to one another such so they have a second configuration. The second configuration may involve non-alignment of container 718 and insertion mechanism 724 as illustrated in Figure 25, or, in alternative embodiments, axial alignment of container 718 and insertion mechanism 724, or any other relative position of container 718 and insertion mechanism 724. In some embodiments, the first configuration is different from the second configuration.
In accordance with another aspect of the disclosure, the fluid path assemblies can be maintained in a sterile condition and the drug containers of each assembly can be aseptically loaded with a pharmaceutical compound using processes similar to those known in the art. After loading a pharmaceutical treatment into the drug container and the container is hermetically sealed, for example with the plunger seal 764 of the embodiment of Figures 27-30, the finish-fill cartridge 716 can be removed from the sterile loading environment without understanding the sterility or integrity of the container of the drug container 718, the fluid path assembly 720 or its individual components.
Alternatively, the fill-finish process may be such that the plunger seal 764 is inserted into the proximal end of drug container 718 prior to filling container 718 with a pharmaceutical treatment. In such an embodiment, the pharmaceutical treatment can be loaded from the distal end 728 of drug container 718 prior to insertion and connection of fluid path connector 722 and fluid path assembly 720. Accordingly, the charge-finish cartridges of the present disclosure allow the fluid path assemblies of the present disclosure to be loaded with pharmaceutical treatments in standard charge-finish processes, greatly reducing the complexities associated with the manufacture and operation of components and drug delivery devices where they are incorporated.
In accordance with another aspect of the disclosure, the embodiments of the charge-finish cartridges of the present disclosure may allow the fluid path assemblies to be loaded in standard charge-finish processes. In this regard, the charge-finish cartridges can use existing or standard charge-finish equipment. A plurality of 716 charge-finish cartridges, as illustrated in Figures 27-30, for example, can be mounted, attached, inserted, or otherwise removably placed on a standard 770 charge-finish tray , as illustrated in Figures 31-32, for loading with pharmaceutical treatments. As explained above, the tab 719 of the drug container 718 can assist in the placement and handling of the refill-fill cartridges 716. The loading-finishing tray 770 illustrated in Figures 31-32 is configured to hold thirty-six drug containers, herein, loading-finishing cartridges 716, but trays of any configuration or capable of containing any number can be used of containers.
In accordance with another aspect of the disclosure, the finish-fill cartridges may be configured to be either fixed cartridges or adjustable cartridges. For example, the cartridges may have a flexible or adjustable portion that allows them to bend, rotate, expand, or contract to accommodate a number of different fluid path assemblies or to fit with load-finish processing trays of different dimensions.
In accordance with yet another aspect of the disclosure, the components of some embodiments of the refill-cartridge cartridges may be incorporated in the drug delivery devices, while in other embodiments, the components of the refill-cartridge cartridges may be used for the charge finishing process, and then discarded after mounting the fluid path assembly and the drug container on a drug delivery device. For example, in one embodiment as illustrated in Figures 27-30 used as shown in Figure 25, by removing the body, the connection collar can be used to mount and / or hold the drug container in place within the drug delivery device, while the needle insertion mechanism is mounted remotely from and at 90 ° from the drug container.
In the embodiment of Figures 33-35, a finishing-charging cartridge 816 is illustrated which includes a vehicle 842 that can be disposed after the loading-finishing process, i.e. prior to insertion into a delivery device. drug. The finished refill cartridge 816 of this embodiment includes a fluid path assembly 820 connected to a drug container 818. Fluid path assembly 820 includes a needle insertion mechanism 824 coupled to a fluid path connector 822 by a fluid conduit 826. A proximal end of needle insertion mechanism 824 is connected to one end. distal of a fluid line 826 which is connected at its proximal end to the fluid line connector 822. In order to provide additional support to the refill-fill cartridge 816, the illustrated vehicle 842 is arranged around the drug container portions 818 and the fluid path assembly 820, i.e. the fluid path connector 822, fluid conduit 826 and a portion of needle insertion mechanism 824.
Vehicle 842 is generally an elongated tubular structure that can be manufactured in multiple components to facilitate assembly and disassembly, if desired. In the illustrated embodiment, a portion of vehicle 842 includes circumferentially extending arms 843 having projections 844, while a mating portion of vehicle 842 includes recesses or openings 846 through which projections 844 can extend when assembled around of the finishing-loading cartridge 816.
In order to help keep the components of the charge-finish cartridge 816 in their relative positions, the vehicle 842 may further include one or more radially protruding flanges 848a, 848b, 848c. As will be apparent from the following explanation, tabs 848a and 848b may be arranged to further secure aspects of the fluid path connector 822 and the drug container 818 in their relative positions. Furthermore, as will also be evident from the following explanation, the tabs 848b and 848c may be arranged to hold the finished-charge cartridge 816 in a non-actuated position during charging, and, optionally, placement within a drug administration. In order to allow actuation of the device, the vehicle 842 can be removed from the charge-finish cartridge 816 and discarded. Vehicle 842 may further include a detachable clamp 840. Detachable clamp 840 may have a generally U-shaped structure and surfaces facing the surfaces of the charge-finish cartridge 816 to prevent premature termination of the fluid path from the container. of drug 818 to fluid path connector 822. Detachable clamp 840 can remain with the refill-fill cartridge 816 when it is assembled in a housing of a drug delivery device; In some embodiments, the structure within the drug delivery device housing may face one or more surfaces of the detachable clamp 840 to cause the detachable clamp 840 to disengage from the refill-cartridge 816 when assembled within the housing.
Drug container 818 is an elongated, generally annular structure, although drug container 818 may be of alternative design. For example, a tab 819 may be provided at any appropriate location along the drug container 818. Said tab 819 may be integrally formed with drug container 818 or it may be a separate element that is attached to drug container 818. In the illustrated embodiment, tab 819 is a separate component that is coupled to a proximal end 827 of drug container 818. In one embodiment, tab 819 can interact with a wall of a drug delivery device housing that incorporates finish-fill cartridge 816 In addition, in this embodiment, a tab 817 is provided at the distal end 828 of drug container 818. As illustrated in Figure 35, the tab 817 can be coupled with the tab 848a of vehicle 842 to facilitate maintaining the relative positions of the components of the charge-finish cartridge 816 during the charge-finish and handling process.
In order to seal the drug container 818, a permeable seal 850 can be provided at the distal end 828 of the drug container 818. In this way, a drug contained within the drug container 818 can be kept in a sterile environment until now. where joint 850 is drilled through fluid path connector 822 to complete the fluid path. Drug container 818 can be assembled with leaky seal 850 and fluid path assembly 820 for sterilization before or after loading. The 850 gasket can be of any suitable design and material. Leaky seal 850 includes a thin membrane 862 or the like that can be perforated to complete the fluid path from drug container 818 through fluid path connector 822 and fluid conduit 826 to needle insertion assembly 824 .
Leaky seal 850 may include a structure that facilitates connection to drug container 818 and / or fluid path connector 822. For example, leaky seal 850 may include a portion 852 that rests within drug container 818. , providing a mating surface for mounting the leaky seal 850 to the drug container 818.
The 822 fluid path connector can be of any appropriate design. Such drilling provisions are disclosed in, for example, United States Application Serial No. 13 / 612,203, and United States Application Serial No. 13 / 796,156, both incorporated herein by reference. .
Referring to Figure 35, the illustrated fluid path connector 822 includes
100 a cannula 858 which is arranged to pierce the membrane 862 of the permeable joint 850 during actuation, the cannula 858 being separated from the permeable joint 850 in the non-actuated position (see FIG. 35) and progressing, respectively, axially in a proximal direction to face and pierce membrane 862 as a result of actuation. In the embodiment shown in Figure 35, the fluid path connector 822 includes a shaft 854 through which cannula 858 extends. A path from cannula 858 attached within shaft 854 extends from the lumen of the cannula. 858 to a lumen of fluid passage 826. Accordingly, when cannula 858 pierces membrane 862 of leaky joint 850, the fluid path is provided between drug container 818, fluid conduit 826, and needle 825 of needle insertion mechanism 824.
In order to keep shaft 854, and thus cannula 858, in a desired position relative to leaky seal 850 by closing drug container 818, fluid path connector 822 further includes a nozzle 853 formed of foldable material, such as an elastomeric material. A distal end of the nozzle 853 includes a generally axially extending hole 853a that is arranged around a portion of the shaft 854, while a proximal end of the nozzle 853 includes a flange 853b that extends generally in the radial direction. Leaky seal 850 may also include a tab 849 which may be sandwiched between tab 853b of nozzle 853 of fluid path connector 822 and tab 817 at distal end 828 of drug container 818. As with the embodiment illustrated in Figures 27-30, a retaining structure, such as a cover 851, may be provided around the periphery of flanges 817, 849, 853b.
The fluid path connector 822 of the refill-fill cartridge 816 can be pierced through the membrane 862 of the leaky seal 850 to complete the fluid path, for example, by manual depression of the proximal end 827 of the drug container 818 or by alternative arrangement. During actuation, nozzle 853 arches outward to allow relative axial movement between shaft 854 and permeable seal 850 such that cannula 858 passes through membrane 862 of permeable seal 850 to fluidly connect the Drug 818 to the delivery needle 825 of the needle insertion mechanism 824 through the fluid line 826.
In order to inhibit inadvertent activation of the fluid path connector 822 once vehicle 842 has been removed, removable clamp 840 may be provided around a portion of the circumference of the sterile nozzle 853 and / or between surfaces that they inhibit axial movement of shaft 854 relative to drug container 818. Detachable clamp 840 may be a relatively rigid structure facing opposing surfaces 840a, 840b, for example, on a surface of shaft 854 and flange
101
853b of the sterile nozzle 853 or, as here, the cap 851 along the flange 853b; as a result, removable clamp 840 inhibits axial movement of shaft 854 relative to joint 850. The illustrated detachable clamp 840 also closely follows at least a portion of the periphery of the sterile nozzle 853; as a result, removable clamp 840 also prevents sterile nozzle 853 from tilting outward when cannula 858 is moved axially to pierce joint 850. In this embodiment, the detachable clamp 840 can be slipped out of position on the sterile mouthpiece 853 by the patient before assembling the refill-cartridge 816 in the drug delivery device or by the action of placement in the delivery device of drug, for example, when detachable clamp 840 engages facing surfaces of the delivery device housing (not illustrated).
The needle insertion mechanism 824 can be of any suitable design. The needle insertion mechanism 824 illustrated in connection with the embodiment of Figures 33-36 also includes a needle retraction mechanism, and is shown and explained in greater detail in US Application No. series 13 / 599,727, which is incorporated by reference.
Insertion mechanism 824 includes an insertion mechanism housing 865 having one or more locking windows 865a, a base 866, and a sterile nozzle 879. Base 866 includes an opening for needle passage 825 and may include a membrane of seal 867 which, in at least one embodiment, can be removed prior to use of the top-fill cartridge 816. Alternatively, the sealing membrane 867 may remain attached to the bottom of the base 866 such that needle 825 pierces the sealing membrane 867 during operation of the charge-finish cartridge 816 within the drug delivery device incorporating the same.
Insertion mechanism 824 may further include an insert deflection member 868, a shaft 869, a needle 825, a refractive deflection member 871, a clip 872, a manifold guide 873, a septum 874, a cannula 875 and a collector 876. As illustrated in FIG. 35, both insertion and retraction deflection members 868, 871 are maintained in excited states. Collector 876 may be connected to sterile fluid conduit 826 to allow fluid flow through collector 876, cannula 875, and into the patient's body during drug administration, as will be described in more detail herein. .
As used herein, Needle 825 is understood to refer to various needles, including, but not limited to, conventional hollow needles, such as rigid hollow steel needles and solid core needles, often referred to as trocars. In one embodiment, needle 825 may be a trocar of
102 27 gauge solid core and, in other embodiments, the needle may be a needle of any size suitable for inserting the cannula for the type of drug and drug delivery (eg, subcutaneous, intramuscular, intradermal, etc.).
During assembly, the proximal end of needle 825 is held in fixed contact with shaft 869. Needle 825 may be positioned to move through cannula 875, if provided, in order to further control movement of the needle. needle 825. Shaft 869, and thus needle 825, is held in selective contact with manifold guide 873 by clip 872. Although deflection members 868 and 871 rest on manifold guide 873, manifold guide 873 is held in position by at least one locking pin 878, which extends through window 865a of housing 865.
The actuation of the needle insertion device 824 results from the removal of the locking pin 878. The locking pin 878 can be removed from the window 865<sup>to</sup>, either directly or indirectly, as a result of actuation of the finished loading cartridge 816. By removing the locking pin 878, the manifold guide 873 carrying the shaft 869 and the needle 825 is allowed to move axially under force to deviation of injection deviation member 868. That is, needle 825 moves to the injection position. As shaft 869 and needle 825 move to the injection position, sterile nozzle 879 folds.
In at least some embodiments, such as the embodiment shown in Figure 35, the needle insertion mechanism 824 further includes a retraction mechanism that retracts the needle 825 after injection. Said retraction mechanism can be of any appropriate design. When manifold guide 873 moves axially in the distal direction, clip 872 releases shaft 869. Upon release, the deflection force of the retraction deflection member 871 causes the shaft 869 and associated needle 825 to retract.
As with the embodiment of Figures 27-30, needle insertion mechanism 824 of Figures 33-36 includes an axially aligned structure such that delivery needle 825 extends axially from a distal end of the cartridge. charges finish 816 during administration. It will be appreciated that the components may be affixed to be affixed by any appropriate structure and method. The relative positions of the fluid path connector 822 and the needle insertion mechanism 824 can be maintained, for example, by a bracket 880, as seen in Figures 34-36. The illustrated bracket 880 extends between the axis 854 of the fluid path connector 822 and the insert mechanism housing 865, as can be seen from the enhancement of Figure 35. The bracket 880 can perform additional functions such as, for example, managing of fluid line 826.
It will be appreciated that, in some embodiments where the 880 bracket is removed from its
103 connection with the fluid path connect 822 or the needle Insertion mechanism 824, or where the refill cartridge does not include the holder 880, the fluid line 826 can provide a flexible fluid connection between the connect of Fluid path 822 and Needle insertion mechanism 824, allowing Needle insertion mechanism 824 and Fluid path connection 822 to be placed in a position other than in axial alignment. Such embodiments are illustrated, for example, in Figure 25 or Figures 37-40.
Referring to FIG. 37, another embodiment of a drug delivery device 910 is illustrated in accordance with the teachings of the disclosure. A portion of housing 912 of drug delivery device 910 is detached to illustrate the relative positions of the components contained therein. Finished refill cartridge 916 Includes a drug container 918 to which a fluid path assembly 920 is attached. Fluid path assembly 920 includes a fluid path connection 922, fluidly coupled to a needle insertion mechanism 924 by a fluid passage 926. It will be appreciated that, in this embodiment, although they remain fluidly coupled , the needle insertion mechanism 924 disengages from the fluid path port 922 of the fill-fill cartridge 916 when assembled in housing 912. As shown in Figures 38 and 39, during the load-finish process, the components align to allow the load-finish cartridge 916 to be easily placed on a tray, as illustrated in Figures 31 and 32 . However, it is observed that the components are not in axial alignment in the loading-finishing cartridge 916 during the loading-finishing process as the axis of the needle insertion mechanism 924 extends perpendicular to the axis of the medicine container. 918 and the fluid path connection 922. As can best be seen in Figure 38, the needle insertion mechanism 924 may include a sealing membrane 967 which, in at least one embodiment, can be removed prior to use of the charge-refill cartridge 916 within the delivery device. of drugs to allow passage of a needle from the needle insertion mechanism 924. Alternatively, the sealing membrane 967 may remain attached to the bottom of the needle insertion mechanism 924 in such a way that the needle pierces the sealing membrane 967 during operation of the charge-finish cartridge 916 within the drug delivery device. 910 that incorporates it.
Referring to FIG. 38, the charge-finish cartridge 916 is illustrated along with a vehicle 942 that partially surrounds the assembled charge-finish cartridge 916 during the charge-finish process. As can be seen in Figure 38, vehicle 942 substantially surrounds a distal portion of drug container 918, connecting fluid path 922 and needle insertion mechanism 924. Vehicle 942 in this embodiment includes three separate sections, although a larger or smaller number may be provided. In this
104 In the embodiment, a portion of the vehicle 942 is disposable prior to placement of the charge-finish cartridge 916 in the housing 912 of the drug delivery device 910, while a portion remains in the charge-finish cartridge 916 when disposed in the housing 912, and can be used in the operation of device 910.
As can be seen in Figures 14 and 15, vehicle 942 includes a first section of leather 941a and a second section of body 941 b. The first and second body sections 941a, 941b can be selectively coupled to each other by any appropriate mechanism. In the illustrated embodiment, a coupling arrangement similar to that illustrated in Figures 33-35 is used such that the first and second sections 941a, 941b can be decoupled and removed prior to placement in housing 912 of the delivery device of drugs 910. Vehicle 942 further includes a collar 940 which, when assembled to the charge-finish cartridge 916, completes the body.
Fluid path connector 922 and needle insertion mechanism 924 may be of any suitable design. The illustrated fluid path connector 922, for example, is as explained with respect to Figures 33-36, and the needle insertion mechanism 924 can also be as described with respect to Figures 33-36. . Referring to Fig. 39, in summary, there is a permeable seal 950 disposed between the drug container 918 and a sterile nozzle 953 of the fluid path connector 922. A cannula 958 extending from an axis 954 is axially disposed within of the sterile mouthpiece 953. Continuous movement of the relative proximal axial cannula 958 toward the leaky seal 950 results in perforation of the leaky joint 950 and termination of the fluid pathway to the needle insertion mechanism 924.
In the assembly of the refill-cartridge 916 in the housing of the drug delivery device 912, the collar 940 remains coupled to the fluid path connector 922, as illustrated in Figure 37. In some embodiments of the disclosure, the vehicle, or a portion thereof, such as collar 940 herein, can be used in the operation or actuation of the charge-finish cartridge 916. In this embodiment, an activation mechanism 914, such as a button, can be provided along an external surface of housing 912 of the drug delivery device to selectively deliver medication to the patient. In this embodiment, trigger mechanism 914 establishes a proximally directed axial force on collar 940. Collar 940 further secures a proximally directed axial force on shaft 954, causing cannula 958 to pierce leaky seal 950 of fluid path connector 922 to complete the fluid path from drug container 918 to the delivery insertion mechanism. needle 924. The needle 924 insertion mechanism can be actuated by any appropriate operation. For example, the movement of a portion of the collar
<img file="MX2018009826A_D0001.tif" />
Xerox WorkCentre 7835 <sup>1</sup>θ5 xprnx of the 924 needle insertion mechanism, as explained in more detail regarding
Detdflé ^ éf «RStídJÍÍ?<sup>gives in</sup> «Auras 33-36. <sub>State of</sub> job:
Now referencing the re ^ lzggóp fdrfMMlffi<sup>3</sup>Finish 1116 includes a drug container 1118 that has both proximal and distal ends 1127, so please report the proximal 1127 may include P <e * w tab 1119 and eSté4adapt®Mltf> to receive a
Device Name: Xerox Ctarke Marks Status Details: Job canceled by user.
Debugger date or gasket of 1164 plunger, while nbqidfiisietieextreme remote128 may include a Shipping time: 11:23 Server name: 192.168.3.6:445 tab 1117 and is adapted to receive 1150 permeable joint together with a fluidq ^^^ l assembly of the® · ^^ 1120 incIt ^ fjg ^ ftQpector of the path of ^^^ uido 1122 and an ^ j ^ nism of Insertion fluidly coupled by a <sub>Λ</sub> fluid line 1126. ~ <sub>r</sub>
File Options Destination Z Status__
Format: In <sub>and</sub>si0f feáUzaetón, the connecting éfé'lfeF'W'ífe fluid 1122 is integrated with the gasket
Multipygy Friendly Name:
Pemperable images of drug container 1118. S ^ rt'teettí'F of fluid path 1122 can be seen Archived Bytes: 0 Best path in cross-sectional view of Figure 41 and exploded view of the □ Exploration actions Norma to archive:
ii% gene ^ 9M / Các43. Fluid Path Connector 112Ió<sub>1</sub>HBfeluyieüMrane assembly of the 1156 shaft having a c & riose '^^ 1154 and a t ^ f ^ X ^^ Ona cannula 1158 is attached to the 1154 shaft to provide a path for the So2PW<sup>nál through canal</sup> <IO & aM<sup>26</sup> P<sup>can</sup> feed to the cannula 1158
M & S ^ al ^ r? ^<sup>e cua</sup>*<sup>c</sup>l<sup>or</sup>'t ^? t<sup>njc</sup>t<sup>ur</sup>to appropriate. Ei ^ 8 | ¡^ | ^ zation, fluid line 1126 is in contrast ^<sub>CO</sub>p |<sub>ac</sub>|<sub>0 to one</sub> TetffiaH 159 that is open QéPmanera fluid to cannula 1158.
Definition: Normal Protocol:
2 © uraaón: With eWm ° to maintain the assembly<sup>i</sup>Efel<sup><:</sup>axis<sup>to the</sup>t 156 together with the associated cannula 1158
Printed faces: larra Document name:
Resolving position with retention to the 1150 permeable gasket, 1130 gasket support is provided. Bits per pixel: 1 color of mr. While the seam of the 1130 gasket may: be coupled to a 1150 permeable gasket ^^ pe3ían ^ whichever ^ ^ s? proper structure, in ^^ §j§§ lustrated region, the 1150 permeable joint and the 1130 joint support includes a est ^ yg ^ jra<sup>s</sup>3rd coupling in the form of respective locking tabs 1131,1132. ^<sup>01000</sup>^ <sup>r</sup> Standard for filing:
Although the shaft assembly 1 'H3B ^^ blílS<sup>n</sup>Yes<sup>l</sup>be assembled with the gasket holder
1130 and the leaky seal 1150 for coupling to the drug container 1118, the leaky seal Destination 5: Status ................
1150 and the gasket support 1130 are slideable in relation to the friendly Name:
shaft assembly 1156. To allow for this non-slip challenge, although coupled, shaft 30 1154 includes one or more elastic poles ll ^ iaid which have surfaces interconnecting with a hole 1160 arranged complement ^ and ^^^^ p,<sub>t</sub>gl gasket holder 1130. As shown in Fig. 41, when gaskets are assembled, cannula 1158 is arranged underlying the membrane 1162 of the gasket ^ g. ^ In this way, ^ "ftirrtarpermeable 1150, the assembly of the 1130 gasket and dáf assembly<sup>3l</sup>W | 8<sup>c</sup>aerial & f9late 1156 form a track connector
Name of the integrated fluid server 1122 that can be assembled to the distal end 1128 of container 1118. Protocol:
In order to further facilitate the »» wftblajiftiidel fluid path connector 1122 al
Document name:
© 2013 Xerox Corporation All rights reserved.
Xerox® and Xerox with the figurative mark® are registered trademarks of Xerox Corporation in the United States and / or other countries.
106 container 1118, a cap 1151 may be provided. One or more gaskets 1133 may be provided between adjacent surfaces of the fluid path connector 1122 and, for example, the flange 1117 of the drug container 1118. One such basket 1133 is illustrated in Figure 41, although additional gaskets may be provided.
The needle insertion mechanism 1124 can be of any appropriate design, such as, for example, the needle insertion mechanism 1124 illustrated in Figure 35. The cannula 1158 of the fluid path connector 1122 is connected in a manner fluid to needle 425 of needle insertion mechanism 1124 via fluid conduit 1126.
In this embodiment, the fluid path connector 1122 and the needle insertion mechanism 1124 are coupled, for example by mechanical coupling, via complementary wires 1134, 1135. In the illustrated embodiment, the fluid path connector 1122, herein, shaft 1154, includes external threads 1134, while the needle insertion mechanism 1124, herein, a hole 436 of a extension 1137 of the insert mechanism housing 1165, includes complementary internal threads 1135. It will be appreciated that alternative arrangements are provided. For example, the threading arrangement could be reversed, the fluid path connector 1122 including internal threads, and the needle insertion mechanism 1124 incorporating external threads. Alternatively, a threaded collar, or the like, could be provided to couple the components together.
Furthermore, although the fluid path connector 1122 and the needle insertion mechanism 1124 are coupled in axial alignment to the charge-finish cartridge 1116 for the charging process, the components could alternatively be arranged. For example, the axis of the needle insertion mechanism 1124 could be arranged at right angles to the axis of the fluid path connector 1122 and the drug container 1118.
In accordance with another aspect of the disclosure, the finish-fill cartridge 1116 provides controlled management of the fluid passage 1126. In this embodiment, the threaded coupling of the needle insertion mechanism 1124 and the fluid path connector 1122 it can provide controlled placement of fluid conduit 1126. Disengaged needle insertion mechanism 1124 and fluid path connector 1122 are illustrated in Figure 44. As the needle insertion mechanism 1124 and the fluid path connector 1122 are threaded together at the positions illustrated in Figures 40 and 41, the fluid passage 1126 is wound around housing 1165 of the insertion mechanism of needle 1124. While the needle insertion mechanism 1124 and the fluid path connector 1122 are illustrated in a disassembled configuration with the fluid path connector 1122 assembled to container 1118 in Figure 44, it will be appreciated that the components can be assembled in any order. For example, the 1124 needle insertion mechanism
107 and fluid path connector 1122 can be assembled together prior to coupling fluid path connector 1122 to container 1118 to form finish-fill cartridge 1116.
Returning to the illustrated embodiment in Figures 45-47, the illustrated refill cartridge 1216 is similar in operation to the refill-finish cartridge 1116 of Figures 40-44. The charge-finish cartridge 1216 of Figures 45-47 differs, however, in that the fluid path connector 1222 is coupled to the needle insertion mechanism 1224 by means of a spring connection 1238, the insertion mechanism of needle 1224 and fluid path connector 1222 which includes a complementary structure that allows components to engage. For example, housing 1265 of needle insertion mechanism 1224 may include an extension 1237 having a recess or hole 1236, or female part, adapted to receive a corresponding male portion 1234 of fluid path connector 1222. To ensure the axial alignment of Extension 1237 and male portion 1234, each may have one or more facing shoulders. For example, recess 1236 which may include shoulders 1282,1284 against which one or more protrusions that extend toward shoulders 1283,1285 of fluid path connector 1222 are seated. To facilitate connection, shaft 1254 Fluid path connector 1222 may include one or more elastic fingers 586 extending from shaft 1254. During assembly, fingers 586 can be bent in such a way that shoulders 1283 can generally move radially inward when fingers 586 move through recess or hole 1236 and snap outward in engagement with shoulders 1282 when the fluid path connector 1222 and needle insertion mechanism 1224 are in their final mounted axial positions. It will be appreciated, however, that the snap connection 1238 may have an alternative structure such as if the fluid path connector 1222 includes a shoulder recess and the needle insertion mechanism 1224 includes shoulder engagement that extend outward.
As with the embodiment of Figures 40-44, the embodiment of the Figures allows controlled management of fluid conduit 1226 that fluidly connects fluid path connector 1222 and needle insertion mechanism 1224. For example , the conduit may be wound around the periphery of housing 1265 of needle insertion mechanism 1224, as illustrated in Figure 47, before, after, or during engagement of snap connection 1238.
Although a threaded connection has been described with respect to Figures 40-44, a snap connection with respect to Figures 45-47, it will be appreciated that alternative mechanical connections can be used to provide sufficient structural integrity to the cartridge to facilitate container loading. in a conventional loading-finishing process. For example, a tongue and groove type connection can be used. As an alternative or
108 Additionally, an external support can be used, such as support 880 of Figures 3336 or relative positions can be maintained by means of a vehicle, such as vehicle 742 of Figures 27-30. Other mechanical coupling devices are also within the scope of the disclosure.
Therefore, it will be appreciated that the inventive arrangement described in the present invention provides varied component designs that can be assembled in various configurations to provide various charge-finish cartridge designs that can be sterilized and loaded in conventional charging processes. finish.
As a further advantage, because the embodiments of the present disclosure allow the manufacture of pre-filled infusion or injection pumps, these pumps can be configured to be single-use or reusable pumps. For example, the fluid path assemblies and / or the charge-finish cartridge of the present disclosure may be configured to be cartridges that can be replaced in reusable pump devices.
Some embodiments of the present disclosure allow the drug container to be charged in a standard charge-finish process, without the need to expose the drug treatment to sterilization or environmental conditions. However, some drug treatments are able to withstand sterilization conditions without degrading, losing efficacy, or the like. Accordingly, in at least one embodiment of the present disclosure, sterilization of the fluid path assembly and / or the fill-fill cartridge can occur after the components have been assembled and the drug container has been filled with a pharmaceutical treatment. This method of manufacturing, loading, and using the new embodiments of the present disclosure may still provide the benefit of being adaptable to a standard loading-finishing standard process. In addition, this method allows manufacturers of drug and filler delivery devices the benefit of only needing to sterilize the components of the fluid pathway (i.e., components that may come into contact with the drug fluid). The finish-fill cartridges, fluid path assemblies, and individual components of the present disclosure can be sterilized prior to integration into a drug delivery device. As such, the other components of the drug delivery device that generally never come into contact with the drug fluid do not need to be sterilized due to the advantages offered by the present disclosure. Accordingly, the embodiments of the present disclosure allow for more complex geometries and more standard materials to be used, for example, for the manufacture of advanced drug delivery devices.
New novel configurations of fluid path assemblies and
109 Refill-finish cartridges of the present disclosure can provide substantial benefits in the market. Embodiments of the present disclosure can be easily manufactured in a sterile environment, integrated into the lines of the standard drug loading process (eg, filler-finishing) for aseptic loading of pharmaceutical treatments, and used for cost-effective assembly in drug devices. drug administration. Each of these advantages has substantial benefits over existing methodologies.
For example, because the fluid path assemblies themselves can be sterilized and kept in a sterile condition during the loading and assembly processes of the devices, the resulting drug delivery device need not be sterilized after assembly (i.e. terminally sterilized). This avoids a number of known challenges facing existing methodologies for the manufacture of drug delivery devices.
Conventional drug delivery devices often require a charge at the time of use because terminal sterilization of the device cannot be completed with the pharmaceutical drug inside the drug container. Various pharmaceutical drugs cannot withstand the temperatures, pressures, and other conditions necessary for sterilization of the device after assembly. In other words, because existing manufacturing processes require sterilization of the entire device, the drug cannot be "preloaded" not within the device prior to sterilization. This adds a complex stage after final assembly of the device, which often requires additional expensive equipment, manipulation of separate drug containers, and / or patient training to perform the loading stage themselves prior to injection. Instead, the embodiments of the present disclosure allow the manufacture, assembly, and use of preloaded drug delivery devices that maintain the sterility of the fluid path assembly through the various manufacturing steps.
Furthermore, because the drug delivery devices incorporating the new embodiments of the present disclosure do not need to be terminal sterilized, the components of the devices may comprise other materials, often less expensive, that would not normally withstand the sterilization environment. For example, less expensive plastics can be used for certain components of the device because they do not need to be sterilized after assembly.
In other words, the embodiments of the present disclosure may allow the manufacturer to sterilize only those components that will be in contact with the drug fluid and / or that are necessary to keep the fluid pathways sterile. These embodiments may also allow the pharmaceutical filler to maintain the sterility of these components during the loading and finishing steps associated with assembling the components.
110 drug delivery devices. Similarly, the drug delivery devices incorporating the fluid path assemblies of the present disclosure may have smaller or more efficient geometries, since the device does not have to be configured for sterilization after assembly.
Additionally, the embodiments of the present disclosure allow the use of standard fill-finish processes to load the drug container. This greatly simplifies the manufacturing processes used to build the drug delivery devices. Standard loading-finishing processes use trays that contain multiple drug containers, such as syringes. Embodiments of the present disclosure allow a manufacturer of drug delivery devices, a pharmaceutical company, or a contract drug loader to load drug containers for infusion or injection pumps using the same standard fill-finish processes. These drug containers can be aseptically loaded, as is standard industry practice, in a cost-effective manner that preserves the sterility of the fluid path assembly. After the fluid path connecting mechanism assembly, the combination assembly can be attached to a drug delivery device without having to sterilize the rest of the device components. Accordingly, the embodiments of the present disclosure can provide new components that allow fluid pathway assemblies to be sterilized, assembled, loaded, and incorporated into drug delivery devices in a cost-effective and streamlined process.
Additionally, the fluid path assemblies of the present disclosure utilize materials that are substantially nonreactive with therapeutic fluids or drugs and are suitable for use in pharmaceutical grade applications. New fluid path assemblies and charge-finish cartridges are configured to minimize or eliminate the possibility of contact or interaction between degradable materials, such as certain plastics, with therapeutic fluids or drugs. Fluid path assemblies, with adaptive needle injection and retraction mechanisms, can also provide fluid conduits from the drug container to the patient, through the needle or cannula, which are substantially devoid of degradable materials. Such configurations, when integrated into refill cartridges or drug delivery devices, can provide stability and longer shelf life parameters to the drug and drug delivery devices. These characteristics are believed to be highly desirable for, in general, all pharmaceutical treatments, but perhaps especially of value in drug delivery devices for use with biologics and other complex therapies.
One or more embodiments of the present disclosure may further include certain
111 standard components. For example, the refill-cartridge cartridge configurations and drug delivery devices of the present disclosure may include one or more membranes. In at least one embodiment, one or more permeable membranes are employed to seal the drug container and / or to ensure a sterile environment and the integrity of the container within the drug chamber. Similarly, the drug container can include a tab. The tab can be preformed along any part of the container, or it can be a separate component that is connected or attached to the container. In at least one embodiment, the tab is a removable connected component that is connected at the proximal end of the drug container. The flange may be configured to allow the charge-finish cartridge and drug container to rest within a charge-finish tray, to fill with a pharmaceutical compound within a standard charge-finish process. The position, shape, number, and materials for such components can be varied, as would be readily appreciated by one skilled in the art, to satisfy any number of desired characteristics.
Similarly, although the components of the finish-fill cartridge and the fluid path assembly are described herein as separate components, it is contemplated in the present disclosure that certain groups of these components may combine to form a single component. capable of performing the functions of individual components. In at least one embodiment, the needle insertion and needle retraction mechanisms can be a unified component that can provide a dual function. Additionally, as one skilled in the art will appreciate, the components of the devices can be manufactured as individual components or as single components. For example, the tab may be a component that is preformed, during the manufacturing process, as a part of the drug container itself. Accordingly, in at least one embodiment, the flange can be an extension of the glass flange of the container. Furthermore, although the components of the charge-finish cartridge and the fluid path assembly are described herein as separate components, they may be unified components having multiple functions. The configuration of the components and their assembly may vary depending on the assembly process, the parameters of the device and other desired characteristics.
Embodiments of the present disclosure can provide fluid path assemblies, refill cartridges, manufacturing methods for such cartridges, and their methods of use. Finish-fill cartridges and fluid path assemblies can be used in a number of different configurations and may themselves comprise one or more components. Such modifications are contemplated and encompassed in the embodiments of the present disclosure. Other components may also be unique components,
112 unified components or multipurpose components, as described in the embodiments discussed above. Therefore, the present disclosure is intended to cover the modifications and variations of the present disclosure, provided that they are within the scope of the appended claims and their equivalents.
Vile. Activation Mechanism
In the following, an activation mechanism 9000 is described in relation to Figures 74 and 75 that enables a user (eg, a self-administered patient) to activate one or more mechanisms or subsystems of a drug delivery device disclosed in this document (eg, drug delivery device 10, 910, 2010, 6000, or 8000). Trigger mechanism 9000 can be configured to trigger, simultaneously or sequentially, one or more of: a trigger mechanism (eg, trigger mechanism 100, 500, 1000, or 2100); a needle insertion mechanism (eg, the needle insertion mechanism 200, 624 or 724); a fluid path connector (eg, the fluid path connector 300, 622, 722, 822, 922 or 2300); and / or a power and control system (eg, the 400 or 2400 power and control system).
Figures 74 and 75 illustrate that trigger mechanism 9000 may include a button 9010 that may correspond to start button 14 or 2014 and a trigger assembly 9020. Button 9010 can protrude from housing 12, such as through a opening between the top of the housing 12A and the bottom of the housing 12B, and can be manually moved by a user, such that the button 9010 can be pressed into the housing 12 by the user. In at least one embodiment, button 9010 may be configured to slide back and forth in a linear direction that is orthogonal to an outer surface of housing 12 from which button 9010 protrudes.
In general, trigger assembly 9020 can be configured to transfer, convert, and / or transmit movement of button 9010 into motion that activates one or more of a drive mechanism, a needle insertion mechanism, a fluid path connector and / or a power and control system. In at least one embodiment, in response to movement of the button 9010 by the user, the trigger assembly 9020 can be configured simultaneously or sequentially: 1) activate a needle insertion mechanism (eg, needle insertion mechanism 200 , 624 or 724) such that the needle insertion mechanism inserts a needle (eg, needle 214) and / or a cannula (eg, cannula 234) into a patient; (2) activate a fluid path connector (eg, fluid path connector 300, 622, 722, 822, 922, or 2300) to establish fluid communication between a drug container (eg, container 50 , 618, 718, 818, 918, 1118, or 2050) and the insertion mechanism; (3) activate a drive mechanism (for example, drive mechanism 100, 500, 1000 or 2100) to force
113 a drug (eg, a PCSK9-specific antibody, a G-CSF, a sclerostin antibody, a CGRP antibody, etc.) stored in the drug container through the fluid path connector and insertion mechanism and , finally, in the patient. In at least one embodiment, movement of the button 9010 by the user may also activate a power and control system (eg, power and control system 400 or 2400), simultaneously or sequentially with activation of the insertion mechanism of the needle, fluid path connector and / or drive mechanism. Accordingly, trigger assembly 9020 can allow a user to activate multiple mechanisms and / or subsystems with a single push of button 9010, thereby simplifying the operation of the drug delivery device for the user.
As shown in the exploded assembly view of FIG. 75, the trigger assembly 9020 may include a plurality of interconnected and / or cooperating components including a trigger arm 9030, a first control arm 9032, a second control arm control 9034, a button spring 9036, a main spring 9038 and a latch 9040 The trigger arm 9030 can be directly connected to the button 9010 so that the trigger arm 9030 and the button 9010 move together as a single unit. Button spring 9036 may be disposed between trigger arm 9030 and first control arm 9032; and the main sliding spring 9038 can be arranged between the first control arm 9032 and the housing 12. In at least one embodiment, the button spring 9036 and the main slide spring 9038 may be arranged in series and parallel to each other, with the control arm 9032 arranged between them. The main slide spring 9038 may have a stiffness that is greater than that of the button spring 9036. Accordingly, initial displacement of the button 9010 by the user can cause the spring of the button 9036 to compress between the trigger arm 9030 and the first control arm 9032; however, due to its increased rigidity, the main slide spring 9038 may not compress between the first control arm 9032 and the housing 12 during the initial movement of the button 9010. Further displacement of the button 9010 by the user may cause the individual coils of the button spring 9036 to contact each other, making further compression of the button spring 9036 extremely difficult or impossible. Accordingly, further displacement of the button 9010 Button 9010 can cause the main slide spring 9038 to compress between the first control arm 9032 and housing 12. Consequently, the first control group 9032 can move in response to the displacement of the button 9010 only after the spring of the button 9036 has been sufficiently compressed. The interaction between the button spring 9036 and the main slide spring 9038 and the resulting movement of the first control arm 9032 can be referred to as a point of no return feature of the button 9010.
114
The delay provided by the 9010 button no-return feature gives the user time to affirm their intention to activate the drug delivery device. Additionally, the button 9010's no-return point feature reduces the risk of accidental activation and provides the user with tactile feedback that informs the user that activation is approaching when the button spring 9036 becomes increasingly compressed.
The first control arm 9032 can be slidably connected to the housing 12 so that the linear displacement of the button 9010 causes the linear displacement of the first control arm 9032. The second control arm 9034 may be rotatably connected to the first control arm 9032 and rotatably connected to the housing 12 so that linear displacement of the first control arm 9032 causes rotation of the second control arm 9032 relative to the first control arm 9032 and to housing 12.
The first control arm 9032 may be configured to interact and activate both the fluid path connector and the needle insertion mechanism. The first control arm 9032 may include a main body 9042 extending along a longitudinal axis A and a first boss 9044 and a second boss 9046 extending from opposite sides of the main body 9042 away from longitudinal axis A. During operation, arm 9032 can slide in a direction that is parallel to longitudinal axis A. In at least one embodiment, the first boss 9044 and the second boss 9046 can each extend orthogonally to longitudinal axis A. By arranging the first and second protrusions 9044 and 9046 on opposite sides of the main body 9042, the first and second protrusions 9044 and 9046 can be used to activate mechanisms located on opposite sides of the drug delivery device. Accordingly, the first and second protrusions 9044 and 9046 can facilitate an arrangement that reduces the overall size of the drug delivery device.
The first protrusion 9044 of the first control arm 9032 can be configured to contact and move a portion of a fluid path connector such that fluid communication is established between a drug container and an insertion mechanism. For example, the first protrusion 9044 can be configured to contact and move connection shaft 310 of fluid path connector 300 toward drug container 50 in response to the displacement of button 9010. Consequently, piercing member 330 mounted on connecting shaft 310 can pierce pierceable seal 56 and access the interior of drug container 50, thereby establishing fluid communication between drug container 50 and the drug insertion mechanism. needle 200 through fluid path connector 300. An example of linear motion imparted to connection shaft 310 by first boss 9044 is illustrated by Figures 4A and 4B.
115
The second protrusion 9046 of the first control arm 9032 can be configured to contact and move a part of a needle insertion mechanism such that the needle insertion mechanism inserts a needle and / or a cannula into the patient. For example, the second protrusion 9046 may be configured to contact and move the locking pin (s) 208 (i.e., the second retainer) so that they no longer occupy the holding position illustrated in Figure 11A. As a result, insert deflection member 210 can be allowed to deactivate and insert needle 214 and cannula 234 into the patient, as shown in FIG. 11B.
The second control arm 9034 may be configured to contact and move a part of a drive mechanism such that the drive mechanism discharges a drug from the container. For example, rotation of the second control arm 9034 caused by linear displacement of the first control arm 9032 can result in the second control arm 9034 moving the clip 2115 (i.e. the first retainer) from its retention position! Shown in Figure 23A. Accordingly, the piston bypass elements 2106, 2122 can be allowed to deactivate and move the piston seal 2060 to discharge the drug from the distal end of the drug container 2050 and ultimately to the patient. In the embodiment illustrated in Figure 74, linear movement of the first control arm 9032 away from the side of the housing 12 having the button 9010 can cause clockwise rotation of the second control arm 9034. A radial protrusion 9048 extending from a central portion 9050 of control arm 9034 may be connected to clip 2115 (not shown) such that clockwise rotation of radial protrusion 9048 moves clip 2115 from its holding position to its release position.
Still referring to Figures 74 and 75, the activation mechanism 9000 may incorporate one or more safety features to prevent premature and / or inadvertent activation of the drug delivery device. In at least one embodiment, the trigger mechanism 9000 may include a body contact sensor 9052 to detect contact between the lower housing 12B and the patient's skin. In at least one embodiment, the body contact sensor 9052 may correspond to the sensor 24 on the body illustrated in Figure 1C. The body contact sensor 9052 may include an interlock 9054 rotatably connected to the lower housing 12B and the interlocking spring 9056 configured to deflect a portion of the interlock 9054 through an opening 9058 in the Lower housing 12B. Contact between the lower housing 12B and the patient's skin can cause the latch 9054 to retract within the housing 12 against the deviation force of the latching spring 9056. When the latch 9054 protrudes from the housing 12B through opening 9058, the
116 Latch 9054 may occupy a locked position where lock 9054 obstructs the linear displacement of trigger arm 9030, as illustrated in Figure 74. Consequently, a user may be unable to press button 9010 when latch 9054 is in its off position. blocking. When the latch 9054 retracts into the housing 12 due to contact with the patient's skin, the latch 9054 can be moved to an unlocked position where the latch 9054 does not obstruct movement of the trigger arm 9030. Consequently, when the latch 9054 occupies its unlocked position, the user may be able to press the button 9010 and activate, via the trigger assembly 9020, one or more of the actuation mechanism, the needle insertion mechanism, the fluid path connector and / or the supply and control system.
Although the 9052 body contact sensor primarily functions as a mechanical locking mechanism, alternative embodiments may incorporate a body contact sensor that is electrically based such as, for example, a capacity or impedance based sensor that must detect tissue before allowing the activation of the power and control system. In at least one embodiment, such a sensor on the electrical body may incorporate a resistance with an impedance of approximately (eg, ± 10%) 1 ΜΩ.
VIII. Additional Embodiments of the Fluid Path Connector
At least some of the drug delivery devices described in the present application, including at least those described in connection with Figures 1-47, 74, 75, and 77-91B, may be configured to incorporate the connector embodiments of the fluid path described below in relation to Figures 48-56 and 76A-76C.
In the loading processes of drug containers and other drug delivery devices, it is sometimes necessary to connect two or more sterile components or subassemblies. For example, portable drug injectors or pumps may include a drug container that can be filled with a fluid drug using standard pharmaceutical fill-finish processes. After charging the drug container, it may be necessary to connect the drug container to one or more additional components or subassemblies such that fluid communication can be established between the drug container and these components. Maintaining the fluid pathway in an aseptic condition is critical, avoiding the introduction of harmful microbes into the drug and / or fluid pathway. The connection of two or more aseptic components or subassemblies is typically performed in an aseptic environment, such as a clean room, thereby ensuring that no harmful microbes are introduced into the assembly. This, however, can lead to a higher manufacturing cost of the drug delivery devices.
Embodiments of the present disclosure allow aseptic connections to be made
117 between two or components or sub-assemblies in a septic environment. As seen in Figures 48A through 48C, connection shaft 310 of the fluid path connector may be connected to drug container 350. Figure 48A shows these components prior to connection. A first film 318 is in place on connection shaft 312. First film 318 covers opening 312B of connecting shaft 312 and prevents microbes from entering cavity 312A through opening 312B, thereby keeping cavity 312B and piercing member 316 in an aseptic condition. Piercing member 316 is partially disposed in cavity 312A and at least partially disposed in retainer 314. Retainer 314 is coupled to connection shaft 312 and can be configured for translation with respect to the connection axis in a direction parallel to the long axis of piercing member 316. The retainer may include one or more locking arms 314A that can engage one or more first recesses 312C on connection shaft 312. The locking arms may include protrusions at their lower end, which in the locked position are at least partially disposed in the upper recesses. The coupling of the flexible arms maintains the spatial relationship of the retainer and the connection axis.
Drug container 350 may include a screw cap 324 that maintains a connection between a pierceable seal 326 and a body (not shown). The pierceable seal keeps the drug fluid inside the body and prevents microbes and other substances from entering the drug chamber. A recess 328 is formed by the geometry of the pierceable seal. A second film 322 is attached to the drug container such that it encloses recess 328, thereby maintaining recess 328 in an aseptic condition. The first and second films can be constructed of any material capable of providing the barrier properties required to maintain the aseptic condition of the associated surfaces. In a preferred embodiment, the films are constructed from an aluminum foil material. Alternatively, the films can be any type of sterilizable membrane, film or sheet. Furthermore, the film can be removable and / or perforable, as well as breathable and / or permeable.
An adhesive can be applied to the exterior surfaces of both the first film 318 and the second film 322 before bonding the fluid path connector and drug container 312. The adhesive may contain antimicrobial, antibacterial, and antiviral compounds to limit or reduce the number of such substances on the joint surface. During connection, flexible arms 312E can engage screw cap 324 or another portion of drug container 312, thereby limiting axial translation of the fluid path connector relative to drug container 312. In this position, the first film 318 and the second film 322 are in contact with, or in close proximity to, each other. If an adhesive is present on the faces of one or more of the films, the films may be
118 linked together.
After the fluid path connector and drug container 312 are joined, the retainer 314 can move axially with respect to the connection axis. The movement of the retainer causes the locking arms 314A to flex and disengage from the first recess 312C. Moving the retainer causes needle 316 to move as well. This translation causes the needle to pierce the first film 318 and the second film 322. After removal of the retainer, the piercing member is at least partially disposed in recess 328 of pierceable 326. The retainer may be further translated, resulting in piercing of a pierceable seal 326 by piercing member 316. After Perforation of the pierceable seal establishes a fluid pathway from the drug container and through the needle. The needle may also be in fluid communication with a conduit, the conduit being configured to transport the contents of the fluid to a delivery mechanism, such as an insertion mechanism to deliver it to a patient. Perforation of the first and second films may occur at the time of assembly. Alternatively, perforation of the films may occur at or near the time of use of the drug delivery device. The patient can initiate perforation of the pierceable seal at or near its time of use by interacting with an activation mechanism.
In some embodiments, the end of the piercing member may remain disposed within cavity 328 until the time of use. The pierceable seal may be configured such that, in response to hydraulic and / or pneumatic pressure within the drug chamber, it deforms and contacts the piercing member. This deformation of the pierceable seal leads to perforation of the joint by the piercing member.
Figures 49A-49D show an embodiment where a connecting axis 1312 of a fluid path connector is connected to a drug container such that the long axis of piercing member 1316 is orthogonal to the long axis of the drug body 1330 of the drug container. As seen in Figure 49B, flexible arms 1312E engage a portion of cap 1324 to securely secure the fluid path connector to the drug container. The fluid path connector may further include insert 1332 disposed within connection shaft 1312. Extension 1314D of retainer 1314 may be tightly coupled to insert 1332 and configured for axial translation with respect to the insert. The projections 1314B of the retainer 1314 are initially arranged in the first recesses 1312C of the connecting shaft 1312. In this position, the piercing end of piercing member 1316 is disposed within insert 1332. Figure 49C shows a cross sectional view of the drug container and fluid path connector after
119 assembly and prior to fluid path connection. As seen in the cross section, the cap 1324 may contain a side port 1324A that allows the piercing member to access the pierceable seal. Also shown in Figure 49C is the conduit port 1314C which may be configured to allow a conduit to connect to the retainer. This conduit can provide a fluid path that connects the drug container to a delivery mechanism for delivery of the fluid drug to the patient. Figure 49D is a cross section showing the assembly in an open fluid path configuration. As shown, the retainer 1314 has moved toward the center axis of the drug container. The projections 1314B of the flexible arms 1314 have been decoupled from the first recesses 1312C and have been coupled to the second recesses 1312D. Piercing member 1316 has pierced first film 1318, second film 1322, and pierceable seal 1326. Perforation of each of these may occur at the time of use when initiated by the patient. Alternatively, the first and second films can be punctured at the time of assembly. This creates a fluid pathway from the drug container, through the piercing member, conduit, and insertion mechanism for administration to the patient. Connecting the fluid path connector such that the long axis of the piercing member is orthogonal to the long axis of the drug container can allow for more compact packaging in a drug delivery device.
In other embodiments, shown in Figs. 50A-50D, the drill element includes an internal drill element 2316A and an external drill element 2316B. The internal drilling element 2316A is arranged within the hollow external drilling element 2316B. After the connection hub 2312 is connected to the drug container 2330, the external piercing member 2316B pierces the first film 2318 covering the terminal end of the connection hub 2312 and the second film 2318 covering the terminal end of the drug container 2330, while maintaining the internal piercing element 2316A within its hollow internal cavity. Perforation can be caused by joint movement of the piercing elements 2316A and 2316B towards the drug container or, alternatively, can be produced by the drug container that displaces the connection hub, thus exposing the external piercing element 2316B. Because the internal piercing element 2316A does not contact the first and second films 2318 and 2322, any contaminants present on the surface of the films 2318 and 2322 do not contact the internal piercing element 2316A. After piercing films 2318 and 2322, the outer piercing member is retracted, thereby exposing the inner piercing member 2316A. In this position, shown in Fig. 50C, the end of internal piercing element 2316A is disposed in cavity 2328 created by pierceable seal 2326. In response to high hydraulic and / or pneumatic pressure within the
120 drug container, pierceable seal 2326 can be deformed, as shown in Fig. 50D. Deformation of pierceable seal 2326 causes internal piercing member 2316A to pierce pierceable seal 2326, thereby creating a fluid path from drug container 2330 through internal piercing member 2316A for administration to the patient.
As shown in the alternative embodiment of Figs. 51-52, the fluid path connector can include an elastomeric component 3334. At least a portion of the external piercing element 2316B can be incorporated into the elastomeric component 3334. The external piercing element 2316B can be incorporated into the elastomeric component 334 while which is in an aseptic environment. The aseptic condition of the built-in portion of the external piercing element 2316B is maintained when the fluid path connection mechanism is transferred to a septic environment due to the sealing fit of the external piercing element 2316B with the 3334 elastomeric component. Therefore, after mounting the fluid path connector with the drug container, the fluid path connector can be transformed into the open configuration by initially piercing the first and second films 2318 and 2322 with the external piercing element 2316B. , and then drilling the pierceable seal 3324 with the inner piercing element 2316A by moving the inner piercing element 2316A relative to the outer piercing member 2316B while the outer piercing member 2316B is held stationary. In this way, the internal piercing element 2316A is not contaminated by touching the non-sterile outer surfaces of the first and second sheets 2318 and 2322. In alternative embodiments, the external piercing element 2316B may be the sole piercing element and / or may pierce the pierceable seal 3324, in addition to the first and second films 2318 and 2322. As seen in the additional alternative embodiment of Figs. 52A-D, the first film 2318 and / or the second film 2322 may further include an adhesive containing antimicrobial agents as described above. Initially, the antimicrobial adhesive of the first film 2318 can be covered by a movable coating 2319 and the antimicrobial adhesive of the second film 2322 can be covered by a movable coating 2323. Before assembling the first film 2318 in cooperation with the second film 2322, they can remove movable liners 2319 and 2323. This presence of the antimicrobial adhesive on the outer surfaces of the first and second films 2318 and 2322 inhibits or prevents contamination of those surfaces if this stage of assembly is performed in a non-sterile environment.
In some embodiments, as shown in Figs. 53A-B, an additional film or gasket 4336 may be present on the outer piercing element 4316B which further isolates the inner cavity of the outer piercing member 4316B and therefore the inner piercing member 4316A. This 4336 gasket can remain intact as the
121 External piercing element pierces first film 4318 and second film 4322. This can prevent any microbes that are present on the joint surfaces from contacting the internal piercing element. After piercing the first and second films 4318 and 4322, the translation of the external piercing element 4318B can be restricted before the external piercing element pierces the pierceable seal EI 4326. Internal piercing element 4316A continues to translate into drug container 2330 and pierces first and second films 4318 and 4322 and pierceable seal 4326, thereby opening the fluid path. Furthermore, in the embodiment shown in Figs. 53A-B, a 4325 antimicrobial adhesive may initially cover the outer surface (s) of the first film 4318 and / or the second film 4322.
In other embodiments, shown in Figs. 54A-C, the first and second films are removed from the fluid path connector and the drug container just prior to mounting of the fluid path connector. Before removal of the films, their placement maintains the sterility of the pierceable seal of the drug container and the face of the elastomeric component of the fluid path connector. Except for the removal of the first and second films prior to connection of the fluid path connector and the drug container and the omission of the external piercing element 2316B, the embodiment shown in Figs. 54A-C includes elements the same or similar to the embodiment shown in Figs. 51A-C. Thus, the same reference numbers are used to indicate the same or similar elements in both sets of figures. It is noted that the external drilling element 2316B of the embodiment shown in Figs. 51 AC can be implemented in an alternative version of the embodiment shown in Figs. 54A-C. Therefore, it is observed that the elastomeric component 3334 of the embodiment of Figs. 54A-C, unlike elastomeric component 3334 of the embodiment of Figs. 51 AC, includes a recess or cavity 2327 configured to receive and form a tight fit (eg, an interference fit or air tight fit) with a distal end 2329 of drug container 2330. This tight fit can prevent entry of contaminants and thus maintain the sterility of the interface between the drug container and the fluid path connector. In some embodiments, the distal end 2329 of drug container 2330 can be inserted into gap 2327 and elastomeric component 3334 under non-sterile or aseptic conditions such that contaminants are not trapped between distal end 2329 of drug container 2330 and elastomeric component 3334 as a result of assembly.
As shown in the alternative embodiment of Figs. 55A-D, the fluid path connector can also be mounted to the drug container 2330 using a 2335 glass tube. After mounting, the 2335 glass tube and the retainer surfaces of the elastomeric piercing element or component 3334 and 3324 perforable seal can
122 sterilize using UV sterilization (see Fig. 55C). The glass tube may be in a sealing fit (eg, an airtight seal) with both drug container 2330 and elastomeric component 3334 of the fluid path connector such that after sterilization microbes and others Foreign elements are unable to enter the glass tube, thus maintaining the aseptic condition of the interior of the glass tube 2335. Except for the omission of the first and second sheets 2318 and 2322 and the inclusion of the glass tube 2335, the embodiment shown in Figs. 55A-D may include elements the same or similar to those of the embodiment shown in Figs. 54A-C. Therefore, equal reference numbers are used to indicate the same or similar elements in both sets of figures.
The embodiment shown in Fig. 56 shows a connection that becomes orthogonal to the long axis of the drug container. In this embodiment, a first film 5318 is initially in place and maintaining the sterility of a cavity 5312A of the connection hub 5312. During connection, the first film 5318 is punctured by an insert 5340 of the drug container. The pierced portion is retained within the concave portion 5342 of the Insert after piercing. By retaining this perforated portion within the concave portion, the non-aseptic surface of the first film is isolated and any substance present thereon is prevented from contaminating the drug fluid or fluid pathway. A second film 5322 is initially in place over an opening 5340A in insert 5340, maintaining the aseptic condition of the opening. The second film 5322 can be a rigid or elastomeric component that is in airtight compliance with the insert so that it prevents microbes and other contaminants from entering the opening. After mounting the connection hub to the drug container, the second film can be displaced from its initial position, thus allowing a fluid path of the drug container to be established through the fluid path connector. After mounting the connection hub to the drug container, opening 5340A in insert 5340 aligns with an opening 5312B in connection hub 5312. A pierceable seal may be in place over one or more of the openings that can be drilled by a drilling element to establish a fluid path. One or more insertion arms may hold the insert in position relative to the drug cylinder. The insertion arms can connect with the drug cylinder itself or another component of the drug container.
While many of the previously described embodiments of the fluid path connector incorporate a piercing element that moves to access the drug container upon activation of the drug delivery device, alternative embodiments of the fluid path connector, such as the embodiment illustrated in Figs. 76A76C, may include a piercing element that remains stationary throughout the administration of the drug. In such alternative embodiments, the drug container can
123 move towards the stationary piercing element upon activation of the drug delivery device. Movement of the drug container can cause the stationary piercing element to access the drug container through the pierceable seal located at the distal end of the drug container.
Figs. 76A-76C illustrate a subassembly of a drug delivery device (eg, drug delivery device 10, 910, 2010, 6000, or 8000) that includes a 10050 drug container (which may be replaced by one or more of drug containers 50, 618, 718, 818, 918, 1118, 2050 or 6050), a drive mechanism 10100 (which may be replaced by one or more of drive mechanisms 100, 500,1000 or 2100) and a fluid path connector 10300. Drug container 10050 may include a cylinder 10058, a plunger seal 10060 movable through cylinder 10058, and a pierceable seal 10056 covering an open distal end of the cylinder 10058 and that controls access to the interior of cylinder 10058.
The drive mechanism 10100 may include a drive housing 10130, a piston 10110 movable with respect to the drive housing 10130 and configured to impart movement to the piston seal 10060, and a piston thrust element 10106 disposed between the 10130 drive and 10110 piston. Before administration, the piston thrust element 10106 may be retained in an energized state of the piston thrust element, as shown in Fig. 76A. When the piston thrust element 10106 is released and consequently deactivated (as seen in Figs. 76B and 76C), the piston thrust element 10106 can move piston 10110 and / or piston seal 10060 towards the fluid path connector 10300.
Fluid path connector 10300 can define a sterile fluid path between drug container 10050 and an insertion mechanism (eg, needle insertion mechanism 200, 624, or 724). Fluid path connector 10300 may include a connection hub 10310, a tubular conduit (not shown) that provides fluid communication between connection hub 10310 and the insertion mechanism, a piercing element 10330 (for example, a needle access control) configured to pierce pierceable seal 10056 to establish fluid communication between cylinder 10058 and tubular conduit during drug administration, a cylinder connector 10332 and a flexible sealing element 10334. In some embodiments, the tubular conduit may be a single unitary tube made of a flexible material and may extend directly between connection hub 10310 and the insertion mechanism. In other embodiments, depending on the need to regulate or modify the fluid pressure, fluid flow rate, or other characteristic of the drug, the tubular conduit may include one or more flow restrictors made of a relatively rigid material and connected at opposite ends by flexible tubes
124 connection hub 10310 and the insertion mechanism, respectively.
Still referring to Figs. 76A-76C, the flexible sealing element 10334 can define a sterile chamber 10062 with a collapsible volume between the distal end of the cylinder 10058 and the connection hub 10310. In at least one embodiment, the flexible sealing element 10334 can have a shape generally tapered and function as flexible bellows. A proximal end of flexible seal element 10334 can be clamped between cylinder connector 10332 and a surface of cylinder distal end 10058. At its distal end, flexible seal element 10334 can be connected to connection hub 10310.
Cylinder connector 10332 may have a tubular body portion 10335 configured to fit snugly around a circumferential surface of cylinder 10058, and first and second annular protrusions radially inwardly dependent 10336, 10338 at opposite ends of tubular body portion 10335 . The first annular protrusion 10336 can grip a neck of cylinder 10058 and the second annular protrusion 10338 can hold the proximal end of flexible sealing member 10334 against the surface of the distal end of cylinder 10332.
The connection hub 10310 can be fixed relative to a housing (eg, housing 12) of the drug delivery device so as to prevent connection hub 10310 from moving relative to the housing of the drug delivery device . A distal end of the piercing element 10330 can be rigidly connected to the connecting hub 10310 so that the piercing element 10330 is also fixed with respect to the housing of the drug delivery device. Cylinder 10058 can be slidably connected to the casing of the drug delivery device so that cylinder 10058 can move (eg, move in a linear direction) relative to the casing of the drug delivery device. As cylinder 10058 moves toward connection hub 10310, flexible sealing member 10334 can be elastically or inelastically deformed so as to decrease the volume of sterile chamber 10062, as illustrated in Figs. 76B and 76C.
In a pre-delivery state (Fig. 76A), a proximal end of piercing element 10330 may be disposed within sterile chamber 10062 defined by flexible sealing member 10334. After releasing piston thrust member 10106, the member The piston thrust 10106 may begin to deactivate and thus cause the piston 10110 and the piston seal 10060 to move towards the drilling element 10330. Friction between the piston seal 10060 and the inner wall of cylinder 10058 may cause cylinder 10058, which is slidably connected to the housing, to initially move in a distal direction together with piston seal 10060. Movement of cylinder 10058 causes pierceable seal 10056 to be pierced by piercing element 10330. As
125 As a result, the piercing element 10330 can access the interior of the cylinder 10058 and establish fluid communication between the cylinder 10058 and the connection hub 10310.
Fig. 76B shows that cylinder 10058 continues to move in the distal direction until it contacts a stop element, which in the present embodiment corresponds to connection hub 10310. The reaction force exerted on cylinder 10058 by the stop member overcomes the friction force between piston seal 10060 and the inner wall of cylinder 10058, thus allowing piston seal 10060 to move relative to cylinder 10058 and discharge drug from cylinder 10058 via piercing element 10330. Fig. 76C shows that the movement of the piston seal 10060 stops, thus ending drug delivery, when the piston seal 10060 impacts a portion of the inner wall of cylinder 10058 in the neck of cylinder 10058.
The combination of the 10300 fluid path connection having a stationary piercing element 10330 and the 10050 drug container having a movable cylinder 10058 eliminates the need for a separate mechanism to establish fluid communication with the Interior of cylinder 10058 upon activation of the drug delivery device. Instead, the force of the piston thrust element 10106 is used to move the pierceable seal 10056 in the stationary bore element 10330 to establish fluid communication with the interior of the cylinder 10058. Accordingly, the design and manufacture of the device can be simplified delivery system, and the overall size of the drug delivery device can be reduced.
IX. Motor Driven Medication Delivery Device
Another embodiment of a drug delivery device 6000 is shown in Figs. 57A-57B. Drug delivery device 6000 may include a container 6050 filled with a volume of a fluid (s) for administration to a patient. The fluid (s) may include one or more of the drugs described below, such as, for example, a granulocyte colony-stimulating factor (G-CSF), an antibody specific for PCSK9 (proprotein convertase subtilisin / kexin type 9), an antibody to sclerostin, or an antibody to the calcitonin gene-related peptide (CGRP). In the drug delivery device 6000, one or more of an insertion mechanism, connecting the fluid path, and the drug delivery drive mechanism, are controlled by the rotation of a 6207 motor. Additionally, or alternatively, An escapement mechanism can be used to control the rotation rate of one or more gears. One of the gears may be meshed with teeth 6208 of an insert mechanism housing 6202. As such, the rotation of the gear train controls the rotation of the insert mechanism housing and thus the insertion of the needle into the patient's skin. The operation of the insertion mechanism will be further described herein.
126
X. Additional embodiments of the insertion mechanism
At least some of the drug delivery devices described in the present application, including at least those described in connection with Figs. 1-57B, can be configured to incorporate the embodiments of the insertion mechanism described below in connection with Figs. 58A-68.
In one embodiment, the insert mechanism 6200 includes an insert mechanism housing 6202 having one or more extension arms 6202A, a base 6252, and a sterile boot 6250, as shown in the exploded view of Figs. 58A and 58B. Base 6252 can be connected to assembly platform 20 to integrate the insertion mechanism into drug delivery device 10 (as shown in Fig. 1B) or the drug delivery device (s) 6000. The connection of the base 6252 to the assembly platform 20 may, for example, be such that the bottom of the base is allowed to pass through a hole in the assembly platform to allow direct contact of the base with the patient's body. In such configurations, the bottom of the base 6252 may include a sealing membrane 6254 which, in at least one embodiment, is mobile prior to use of the drug delivery device 10 or drug delivery device 6000. Alternatively, the sealing membrane 6254 may remain attached to the bottom of the base 6252 such that needle 6214 pierces the sealing membrane 6254 during the operation of the drug delivery device 10 or the drug delivery device 6000. As shown in Figs. 58A and 58B, insertion mechanism 6200 may further include a rotational push member 6210, a needle hub 6212, a needle 6214, a retract push member 6216, a sleeve 6220, and conduit 6218. Line 6218 may connect to sterile fluid line 30 or sterile access connection 300 to allow fluid flow through line 6218, needle 6214, and into the patient's body during drug administration, as will describe in more detail herein.
As used herein, "needle" is intended to refer to a variety of needles including, but not limited to, conventional hollow needles, such as a rigid hollow steel needle. Upon assembly, the proximal end of needle 6214 is held in fixed contact with hub 6212, while the remainder of needle 6214 is preferably located within sterile boot 6250. Needle 6214 may further pass through an opening. base 6252E.
Sterile boot 6250 is a collapsible or compressible sterile membrane that is in fixed connection at a proximal end with hub 6212 and at a distal end with sleeve 6220 and / or base 6252. The term "sterile boot" is used to describe a boot within which certain internal components may reside, in one or more stages of operation, in a
127 sterile condition. The boot does not need to be sterile during the entire operation of the drug delivery mechanism or device, and may actually not be initially sterile until assembly and sterilization of certain components has occurred. Additionally, the term "boot" is not intended to mean any specific shape or configuration, but is instead used to describe a component that can provide an interior space within which other components may reside in one or more stages of operation. In at least one embodiment, sterile boot 6250 is held in a fixed connection at a distal end between base 6252 and sleeve 6220. In other embodiments, the sterile boot 6250 is held in a fixed connection at a distal end between the base 6252 and the insert mechanism housing 6202. The base 6252 includes a base opening 6252E through which the needle can pass during operation of the insertion mechanism, as will be further described below. The sterility of the needle is maintained by its initial positioning within the sterile portions of the insertion mechanism. Specifically, as described above, needle 6214 is maintained in the sterile environment of sterile boot 6250. Base opening 6252E of base 6252 can also be closed from non-sterile environments, such as, for example, by a sealed 6254.
FIGS. 59A-59B and 60-62 show the components of the insertion mechanism, according to at least a first embodiment, in greater detail. As shown in Figs. 59A59B, the insert mechanism housing 6202 may be a substantially cylindrical component having an internal chamber within which conduit 6218, case 6212, needle 6214, sleeve 6220, retraction thrust element 6216 and sterile boot 6250 are substantially disposed in an initial configuration. Guide surfaces 6204 (as best seen in Fig. 59B) are located on the internal surface of housing 6202 and are configured to interact with extension arms 6212A of hub 6212. As will be described in more detail hereinafter, rotation of housing 6202 transfers axial movement of hub 6212 by interaction of guide surfaces 6204 with extension arms 6212A of hub 6212. Housing 6202 may further include one or more protrusions 6202A. The protrusion 6202A is configured to connect a proximal end of the rotational push element 6210. The protrusion 6202A can form the recess 6202B in which the proximal end of the rotary push element 6210 can be arranged. In this way, the unwinding and / or the Deactivation of rotational thrust member 6210 causes housing 6202 to rotate about axis A. Rotational thrust member 6210 can be located on the exterior of housing 6202 in a substantially concentric relationship. The distal end of the rotational thrust element can be connected to the base 6252 or other feature of the drug delivery device 10 or the drug delivery device 6000 so as to restrict movement
128 of the distal end of rotational thrust element 6210. Protrusion 6202A, or another feature, may further contact a portion of the sterile access connection during rotation of housing 6202. This contact, in conjunction with rotation of the housing 6202, can be used to initiate piercing of the pierceable seal and thus allow the contents of the drug container to flow through the conduit.
Hub 6212, as seen in Fig. 60, includes extension arms 6212A as described above. It further includes opening 6212B configured to receive a portion of conduit 6218. Opening 6212B allows conduit 6218 to be in fluid communication with needle 6214 for delivery of the fluid drug to the patient. Needle 6214 is securely connected to hub 6212 by bonding, snap fit, or other means known to one of skill in the art.
Sleeve 6220, as shown in Fig. 61, includes grooves 6220A within which extension arms 6212A of hub 6212 are at least partially disposed during operation of the insertion mechanism. These grooves restrict the 6212 hub's ability to rotate. Sleeve 6220 further includes one or more openings 6220B that are configured to interface with flex arms 6252A of base 6252. During assembly, flex arms 6252A connect openings 6220B, thereby restricting movement of sleeve 6220 relative to base 6252. Base 6252, as shown in Fig. 62, may further include one or more alignment elements 6252C configured to connect one or more alignment notches 6220C of sleeve 6220. This connection aligns sleeve 6220 with base 6252 and limits rotation of sleeve 6220 with respect to base 6252. Base 6252 may also include one or more top aligning elements 6252D configured to connect face 206 of housing 6202 during installation, thereby positioning housing 6202 relative to base 6252.
The operation of the insertion mechanism is described herein with reference to the above components, in view of Figs. 63-65. Fig. 63A shows an isometric view and Fig. 63B shows a cross-sectional view of the insertion mechanism, according to at least one embodiment of the present disclosure, in a locked and ready-to-use stage. The proximal end of rotational push element 6210 is disposed in recess 6202B of housing 6202, and rotational push element 6210 is in an energized state. In this initial position, hub 6212 is in a proximal retracted position such that needle 6214 does not extend past opening 6252E of base 6252. Sterile boot 6250 is in an extended configuration with one end connected to hub 6212 and the other connected to wrap 6220 and base 6252. Retracting push element 6216 is in a relatively decompressed and / or de-energized state. The extension arms 6212A of hub 6212 are located within or substantially adjacent to the
129 Proximal portion 6204A of guide surfaces 6204. Coiled fluid line 6218 can be located proximally to hub 6212. Fluid line 6218 can connect at one end to hub 6212, allowing fluid drug content to pass from drug container 50 to the needle 6214 for administration to the patient.
Insertion mechanism 6200 can be maintained in this initial configuration by interaction with other components of drug delivery device 10 or drug delivery device 6000. By way of example, activating element 14 can be connected to a slider which, in An initial setup prevents housing 6202 from rotating by interacting with extension arm 6202A. Pressing the trigger element 14 can displace the slide, disconnecting the slide of the extension arm 6202A from the housing 6202, thus allowing the rotation of the housing 6202. In an alternative embodiment, shown in Figs. 57A-57B, a housing portion 6202 may have gear teeth 6208 configured to interact with a gear 6209 that prevents rotation of the housing. In this configuration, the gear can be connected to a 6207 motor that controls the rotation of the gear and therefore the housing. The housing may be able to disconnect from the gear, thus allowing free rotation of the housing in response to de-energization of the rotational thrust element. The 6209 gear can be connected to the 6207 motor by a gear train, the gear train controlling the relationship between the rotation of the 6207 motor and the 6209 gear. Additionally, or alternatively, an escapement mechanism can be used to control the rotation of the gear train.
FIG. 64A shows an isometric view and Fig. 64B shows a cross sectional view of an insertion mechanism at an inserted stage of the needle. As shown in Fig. 63A, unwinding and / or de-energizing rotational thrust member 6210 causes housing 6202 to rotate about axis A. As housing 6202 rotates, contact of guide surfaces 6204 with arms Extension 6212A of hub 6212 causes hub 6212 to translate in the distal direction. Hub 6212 is prevented from rotating by interaction between extension arms 6212A and grooves 6220A of sleeve 6220. Sleeve 6220 is connected to base 6252 by connection of flex arms 6252B with openings 6220B. As shown, sterile boot 6250 is allowed to fold as housing 6202 rotates and hub 6212 is translated in the distal direction and needle 6214 is inserted into the patient's body. At this stage, shown in Fig. 63B, needle 6214 is inserted into the patient's body for drug administration. Due to the distal translation of hub 6212, retraction thrust member 6216 is compressed or energized. Rotation of housing 6202 is preferably limited or stops in a position where guide surfaces 6204 retain hub 6212 in a distal position. The rotation of the housing 6202 can be stopped in this position by interaction between the protrusion 6202A and a stop component of the
130 drug delivery device 10 or drug delivery device 6000. Alternatively, a stop component can interact with another housing portion 6202. Upon insertion of needle 6214, the fluid pathway from the conduit to the body is opened. the patient through needle 6214. Because the fluid path connector is made to the drug container and the drive mechanism is activated, fluid drug treatment is forced out of the drug container through the fluid path connector and fluid line. sterile on needle 6214 for administration to the patient's body.
As shown in Fig. 65A and 65B, upon completion of drug administration, needle 6214 retracts (ie, moves axially in the proximal direction) in the housing of inserter 6202. Continuous rotation of the housing 6202 aligns proximal portion 6204A of guide surfaces 6204 with extension arms 6212A of hub 6212 so that proximal translation of hub 6212 is no longer restricted. In this position, the retracting push element 6216 is capable of decompressing or de-energizing. Expansion of the retracting push element 6216 translates hub 6212, and needle 6214 to which it is connected, axially in the proximal direction. Accordingly, activation of the insertion mechanism inserts needle 6214 into the patient's body, and sequentially retracts needle 6214 after completion of drug administration or after some other retraction initiation mechanism.
FIGS. 11-13 show another embodiment of an insertion mechanism. As shown in FIG. 66, one end of the rotational push member 7210 is disposed in a gap 7202B formed in the housing 7202 of the insert mechanism. Connecting the housing in this way eliminates the requirement for a protrusion to extend out of the housing, thereby reducing the overall size of the insertion mechanism. Furthermore, as shown in Fig. 67, the 7250 sterile boot can be configured in an "accordion" configuration, which can allow the diameter of the sterile boot to be less than that of the sterile boot shown in previous embodiments. It can also be seen in Fig. 67 that platform 7020 may have an upwardly extending stud 7020A that aids in locating and retaining the needle insertion mechanism. Rotational thrust member 7210 can be positioned around the outside of stud 7020A. The needle insertion mechanism may also include cap 7222. The cap can connect shell 7220 and act to hold the components of the needle insertion mechanism in place. Specifically, the cover can hold the conduit in place within housing 7202. The cap may include one or more circumferential flexing arms 7222A which, during installation, may flex outward in response to contact with shell protrusions 7220. The flexing arms can then return to their natural position and thus be retained in position. place relative to the shell as best seen in the cross-sectional view of Fig. 68. Also seen
131 In Fig. 68, one or more flexing arms 7020B of platform 7020 can connect with openings 7220B in housing 7220. This connection retains and positions the insertion mechanism relative to platform 7020. Platform 7020 of the Drug delivery may further include locking arms 7020B that are configured to connect the openings 7220B of the shell. This connection holds the insertion mechanism in position with respect to the drug delivery device. The operating steps of this embodiment may be substantially similar to those described above (i.e., de-energizing of the rotational thrust element leads to insertion of the needle and de-energization of the retraction thrust element leads to retraction of the needle) .
In some embodiments, retraction is activated upon removal of the drug delivery device from the patient's body. In other embodiments, retraction is activated if it is determined that an error has occurred in the administration of the substances to the patient. For example, an occlusion of the drug delivery route that prevents the drug flow from being detected by a detection function of the drug delivery device. Upon detection of the occlusion, an electrical or mechanical input can be used to initiate retraction of the needle.
Activation of the needle retraction can be carried out through many mechanisms. For example, a button may be provided on the outside of housing 12 which, when pressed by the patient, activates retraction of the needle from the patient's body. For example, in one embodiment, pressing the button may allow housing 6202 to rotate, thereby allowing retraction push member 6216 to expand and retract needle 6214. The actuation of the button may be spring assisted so that the travel and / or force required to press the button is reduced. Alternatively, or additionally, after the actuation mechanism 100 reaches the end of the dose, an electrical or mechanical actuator may cause the retraction to activate. For example, after the end of the dose, an electrical connection can be made so that a current is applied to a nitinol component. After the application of the current, the temperature of the nitinol component increases. Due to the shape memory characteristics of nitinol, this component can be configured, after an increase in temperature, to transform from a first configuration to a second configuration. In this second configuration, the nitinol component can allow or produce the retraction drive of the needle, for example, allowing the housing 6202 to rotate.
Alternatively, or additionally, a sensor such as a sensor in the body 24 can produce or allow, when the drug delivery device 10 is removed from the patient's body, the activation of the needle retraction. For example, when the device
132 delivery device 10 is installed in the patient, the position of the sensor in the body 24 can prevent the housing 6202 from rotating to the retract position. Upon removal of the patient, a change in the configuration of the sensor in the body 24 may allow rotation. In another embodiment, a light sensor can be placed in drug delivery device 10 near base opening 6252. When the drug delivery device 10 is in place in the patient's body, light would be substantially blocked from entering the light sensor. Upon removal of the drug delivery device 10 from the patient's body, light can be detected by the light sensor and the light sensor can trigger an electromechanical actuator to allow or cause retraction activation. In other embodiments, a bolt-type snap fit interface is used to initiate retraction of the needle. The bolt can be tilted to at least partially protrude from housing 12 and move after placement of drug delivery device 10 in the patient. When traveling, the bolt can connect a female hole in a PCB that can be a part of the 400 power and control system. Upon removal of the drug delivery device 10 from the patient, the inclined pin is disconnected from the female PCB port, thereby producing a signal to activate needle retraction.
Certain optional standard components or variations of the 6200 insertion mechanism or 10 or 6000 drug delivery devices are contemplated, so long as they are within the breadth and scope of the present disclosure. For example, upper or lower housings may optionally contain one or more transparent or translucent windows 18, as shown in Figs. 1A-1C, to allow the patient to view the operation of the drug delivery device 10 or verify that the drug dose has been completed. Additionally, the drug delivery device 10 may contain an adhesive patch 26 and a patch liner 28 on the bottom surface of the housing 12. The adhesive patch 26 can be used to adhere the drug delivery device 10 to the patient's body to administration of the drug dose. As would be readily understood by one of ordinary skill in the art, the adhesive patch 26 may have an adhesive surface for adhesion of the drug delivery device to the patient's body. The adhesive surface of the adhesive patch 26 may initially be covered by a non-adhesive patch liner 28, which is removed from the adhesive patch 26 prior to placing the drug delivery device 10 in contact with the patient's body. Adhesive patch 26 may optionally include a protective liner that prevents actuation of the optional sensor in body 24 and covers base opening 6252E. Removal of the patch liner 28 can remove the protective liner or the protective liner can be removed separately. Removal of the patch liner 28 can further remove the sealing membrane 6254 from the
133 insertion mechanism 6200, opening the insertion mechanism to the patient's body for drug administration.
Similarly, one or more of the insert mechanism components 6200 and drug delivery devices 10 and 6000 can be modified, as long as they remain functionally within the scope and scope of the present disclosure. For example, as described above, although the casing of the drug delivery device 10 is shown as two separate components, the upper casing 12A and the lower casing 12B, these components may be a single unified component. As discussed above, a glue, adhesive, or other known materials or methods can be used to secure one or more components of the insertion mechanism and / or drug delivery device to each other. Alternatively, one or more components of the insertion mechanism and / or drug delivery device may be a unified component. For example, the top case and the bottom case may be separate components held together by an adhesive or glue, a threaded fit connection, an interference fit, a fusion joint, solder, ultrasonic welding, and the like; or the upper case and the lower case can be a single unified component. Such standard functional components and variations would be appreciated by one of ordinary skill in the art and are, therefore, within the scope and scope of the present disclosure.
It will be appreciated from the foregoing description that the insertion mechanisms and drug delivery devices disclosed herein provide an efficient and easily operated system for automated drug delivery from a drug container. The novel embodiments described herein provide integrated security features; allow direct activation by the patient of the insertion mechanism; and are configured to maintain the sterility of the fluid path. As previously described, built-in safety features include optional body sensors, redundant locks, automated needle insertion and retraction upon patient activation, and numerous patient feedback options, including visual feedback options and auditory. The novel insertion mechanisms of the present disclosure can be directly activated by the patient. For example, in at least one embodiment, the rotation prevention feature, whether it is a stop component configured to connect the protrusion 6202A or a gear meshed with the teeth of the housing 6202, which maintains the insertion mechanism in its state retracted locked, it is displaced directly from its locked position by the patient pressing the trigger mechanism. Alternatively, one or more additional components may be included, such as a spring mechanism, which displaces the rotation prevention feature after
134 direct displacement of the activation mechanism by the patient without any intermediate stage. In at least one configuration, rotation of a motor produces or allows rotation of a gear, thereby allowing rotation of the insert mechanism housing.
Furthermore, the novel configurations of the insertion mechanism and drug delivery devices of the present disclosure maintain sterility of the fluid pathway during storage, transport, and through operation of the device. Because the pathway through which the drug fluid travels within the device is completely maintained in a sterile condition, only these components need to be sterilized during the manufacturing process. Such components include the drug container of the drive mechanism, the fluid path connector, the sterile fluid line, and the insertion mechanism. In at least one embodiment of the present disclosure, the power and control system, assembly platform, control arm, trigger mechanism, housing, and other components of the drug delivery device need not be sterilized. This greatly improves the manufacturing capacity of the device and reduces associated assembly costs. Accordingly, the devices of the present disclosure do not require terminal sterilization upon completion of assembly. Another benefit of the present disclosure is that the components described herein are designed to be modular so that, for example, the housing and other components of the drug delivery device can be easily configured to accept and operate the insertion mechanism. 6200 or various other variations of the insertion mechanism described herein.
The assembly and / or manufacture of the insertion mechanism 6200, drug delivery devices 10 or 6000, or any of the individual components, can use various materials and methodologies known in the art. For example, various known cleaning fluids such as isopropyl alcohol can be used to clean components and / or devices. Similarly, various known adhesives or glues can be employed in the manufacturing process. Additionally, known siliconization fluids and processes can be employed during the manufacture of the novel components and devices. Furthermore, known sterilization processes may be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
In another embodiment, the present disclosure provides a method of assembling the insertion mechanism that includes the steps of: connecting the tube to a proximal end of a needle; connect a duct to the hub; connect a sterile boot to the bucket; inserting a retraction thrust member into a sleeve of the needle insertion mechanism; inserting the sterile hub, needle, conduit, and boot into the sleeve (in this position, the retracting thrust member is limited between the hub at one end and the shell at the other end);
135 put a casing around the sleeve; inserting a retraction thrust member into the sleeve; and connecting a base to the sleeve by connecting flex arms with openings in the housing. A rotational thrust element can be placed around the housing such that a portion of the rotational thrust element connects to a portion of the housing, thereby coupling de-energization of the thrust element with rotation of the housing.
The distal end of the sterile boot can be positioned and maintained in fixed connection with the distal end of the insert mechanism housing by connecting the housing to a base. In this position, the sterile boot is in an expanded configuration around the needle and creates an annular volume that can be sterile. A fluid line can be connected to the hub so that the fluid path, when opened, runs directly from the fluid line, through the hub, and through the needle. A fluid line connector can be attached to the opposite end of the fluid line. The fluid line connector, and specifically a sterile sleeve of the fluid line connector, can be connected to a cap and pierceable seal of the drug container. The plunger seal and drive mechanism can be connected to the drug container at an opposite end of the fluid path connector. A sealing membrane can be attached to the bottom of the base to close the insertion mechanism from the environment. The components that make up the fluid flow path are now assembled. These components can be sterilized, by various known methods, and then mounted both fixedly and movably on an assembly platform or housing of the drug delivery device.
The manufacture of a drug delivery device includes the step of attaching the base of the insertion mechanism to an assembly platform or housing of the drug delivery device. In at least one embodiment, the joint is allowed to be such that the base of the insertion mechanism passes through the assembly platform and / or housing to come into direct contact with the patient's body. The manufacturing method further includes attaching the fluid path connector, drug container, and drive mechanism to the assembly platform or housing. Additional components of the drug delivery device, as described above, including the power and control system, activation mechanism, and control arm, can be attached, preformed, or pre-assembled to the assembly platform or housing. An adhesive patch and patch liner can be attached to the housing surface of the drug delivery device that contacts the patient during operation of the device.
A method of operating the drug delivery device may include the steps of: activating, by a patient, the activation mechanism; displace an arm of
136 control to operate an insertion mechanism; and actuating a power and control system to activate a drive control mechanism to drive the flow of fluid drug through the drug delivery device. The method may further include the step of: attaching an optional sensor to the body before activating the trigger mechanism. The method may similarly include the step of: establishing a connection between a fluid path connector and a drug container. In addition, the method of operation may include moving a plunger seal into the drive control mechanism and the drug container to force fluid drug flow through the drug container, the fluid path connector, a sterile fluid and the insertion mechanism for the administration of the fluid drug to the body of a patient.
XI. Drug delivery device with multi-function actuation mechanism
Another embodiment of an 8000 drug delivery device is illustrated in Figs. 69A-73D. Various aspects, components, mechanisms, assemblies, manufacturing methods, and methods of use associated with the drug delivery devices described in connection with Figs. 1-68, may be incorporated in and / or applied to the 8000 drug delivery device to the extent that they do not conflict with aspects, components, mechanisms, assemblies, manufacturing methods, and methods of use associated with the 8000 drug delivery device , and vice versa. Furthermore, the drug delivery device 8000 may include a container 8050 filled with a volume of a fluid for administration to a patient. The fluid may be one or more of the drugs described below, such as, for example, a granulocyte colony-stimulating factor (G-CSF), a PCSK9-specific antibody (proprotein convertase subtilisin / kexin type 9), an antibody for sclerostin, or an antibody to the calcitonin gene-related peptide (CGRP).
The present disclosure provides multi-function drive mechanisms for the controlled release of active ingredients, controlled drug delivery pumps with such drive mechanisms, the methods of operation of such devices, and the methods of assembly of such devices. In particular, the multi-function drive mechanisms of the present disclosure allow or initiate various functions, including: (i) controlling the rate of drug administration by measuring, providing resistance, or otherwise preventing free axial translation of the gasket plunger used to force an active ingredient out of a drug container; (ii) activate a needle insertion mechanism to provide a fluid pathway for drug delivery to a patient; and (iii) connecting a sterile fluid pathway to a drug container to allow fluid flow from the drug container to the needle insertion mechanism for administration to the patient. Thus, the novel embodiments of the present disclosure are
137 able to administer active ingredients at variable speeds. The drive mechanisms of the present disclosure may be pre-configurable or dynamically configurable, such as by control by the power and control system, to meet the desired rate or administration profiles, as explained in detail below. Additionally, the driving mechanisms of the present disclosure provide built-in status indication features that provide feedback to the patient before, during, and after drug administration. For example, the patient may provide initial feedback to identify that the system is operational and ready for drug administration. Upon activation, the system can then provide one or more indications of the drug delivery status to the patient. Upon completion of drug administration, the drive mechanism and drug delivery device can provide an end-of-dose indication. Because the end of dose indication is related to the physical end of the axial translation and / or path of one or more components of the actuation mechanism, the actuation mechanism and drug delivery device provide a true indication of the end dose to the patient. Through these mechanisms, confirmation of drug dose administration can be accurately provided to the patient or person administering it. Consequently, the novel devices of the present disclosure alleviate one or more of the problems associated with the devices of the state of the art, such as those mentioned above.
In a first embodiment, the present disclosure provides a multi-function drive mechanism that includes a push button, a gear assembly that includes a main gear, a drive housing, and a drug container that has a cap, a pierceable seal (not visible), a cylinder and a piston seal. The main gear may be, for example, a star gear arranged to contact multiple secondary gears or the surfaces of the gear. A drug chamber, located within the cylinder between the pierceable seal and the plunger seal, may contain a drug fluid for delivery through the drug delivery device and insertion mechanism into the patient's body. A piston, and one or more thrust members, in which the one or more thrust members are initially retained in an energized state and configured to press a piston interface surface, may also be incorporated into the multi-drive mechanism. function. The piston is configured to translate substantially axially within a drug container having a piston seal and a cylinder. A connection is connected at one end to the piston and at another end to a cable / gear drum of a regulating mechanism, in which the joint prevents free expansion of the thrust member from its initial energized state and axial translation
138 free of the piston on which the pushing element presses. The drug container may contain a drug fluid within a drug chamber for administration to a patient. Optionally, a protective sleeve between the push element and the piston interface surface can be used to hide the interior components of the cylinder (namely, the piston and the push element) from view during operation of the drive mechanism. The joint is configured to be released from a cable / gear drum of a multi-function drive mechanism regulating mechanism to measure the free expansion of the thrust member from its initial energized state and the free axial translation of the piston on which press the push element.
In at least one embodiment of the present disclosure, the regulating mechanism is a push-button gear assembly of the multi-function actuating mechanism. The regulating mechanism retards or restricts the distribution of the joint, only allowing it to advance at a regulated or desired speed. This restricts the movement of the piston inside the cylinder, which is pushed by one or more pushing elements, thus controlling the movement of the piston seal and the administration of the drug contained in the chamber. As the plunger seal advances into the drug container, the active ingredient is dispensed through the sterile line connection, conduit, insertion mechanism, and into the patient's body for drug delivery. The push button may be various power / motion sources including, for example, a motor (for example, a DC motor, AC motor, or stage motor) or a solenoid (for example, linear solenoid, rotary solenoid). In a particular embodiment, the push button is a rotary stage motor with a notch corresponding to the gear teeth of the main / star gear.
The regulating mechanism may further include one or more gears from a gear assembly. One or more of the gears may be, for example, compound gears having a small diameter gear attached at a shared central point with a larger diameter gear. The gear assembly may include a cable gear coupled to a cable / gear drum on which the joint can be detachably wound. Accordingly, the rotation of the gear assembly initiated by the push button can be coupled to the cable / gear drum (i.e. through the gear assembly), thus controlling the joint distribution, the expansion rate of the thrust elements. and the axial translation of the piston, and the speed of movement of the piston seal inside the cylinder to force a fluid to leave the drug chamber. The rotational movement of the cable / gear drum, and thus the axial translation of the piston and the piston seal, is measured, restricted or otherwise prevents free axial translation by other components of the regulating element, as described herein. . In particular, the regulatory mechanisms of the present disclosure do not trigger the administration of fluid substances from
139 the drug chamber. The administration of fluid substances from the drug chamber is produced by the expansion of the thrust element from its initial energized state acting on the piston and the piston seal. The regulating mechanisms work in place providing resistance to the free movement of the piston and the piston seal as they are pushed by the expansion of the push element from its initial energized state. The regulatory mechanism does not trigger administration, but only controls the movement of administration. The joint limits or otherwise restricts the movement of the piston and the piston seal, but does not apply force for administration.
In addition to controlling the rate of drug delivery by measuring, providing resistance or otherwise preventing free axial translation of the plunger seal used to force an active ingredient out of a drug container (thereby administering the active ingredients at rates and / or variable administration profiles); The multi-function actuation mechanisms of the present disclosure can simultaneously or sequentially perform the steps of: activating a needle insertion mechanism to provide a fluid pathway for drug delivery to a patient; and connecting a sterile fluid pathway to a drug container to allow fluid flow from the drug container to the needle insertion mechanism for administration to the patient. In at least one embodiment, Initial movement by the push button of the multifunction drive mechanism causes rotation of the main / star gear. In another way, the main / star gear transports motion to the regulating mechanism through the gear assembly. In another way, the star / main gear carries the motion to the needle insertion mechanism through the gear. As the gear rotates through the main / star gear, the gear engages the needle insertion mechanism to initiate the fluid path connector on the patient, as described in detail above. In a particular embodiment, the needle insertion mechanism is a rotational needle insertion mechanism. Accordingly, the gear is configured to connect a corresponding gear surface of the needle insertion mechanism. Rotation of the gear causes rotation of the needle insertion mechanism through interaction of the gear between the gear of the drive mechanism and the corresponding gear surface of the needle insertion mechanism. Once proper rotation of the needle insertion mechanism occurs, the needle insertion mechanism can be started to create the fluid path connector in the patient, as described in detail herein.
In at least one embodiment, rotation of the needle insertion mechanism can thus also result in a connection of a sterile fluid path to a drug container to allow fluid flow from the drug container to the insertion mechanism.
140 needle for administration to the patient. The ramp appearance of the needle insertion mechanism causes it to press down on a movable connection hub of the sterile fluid path connector. As the needle insertion mechanism is rotated by the multi-function actuation mechanism, the ramping aspect of the needle insertion mechanism presses on and moves the movable connection hub of the sterile fluid path connector to facilitate a fluid connection inside. In at least one embodiment, the needle insertion mechanism can be configured such that a particular degree of rotation allows the needle / trocar to retract as detailed above. Additionally or alternatively, such a needle / trocar retraction can be configured to occur upon patient activity or upon movement or function of another component of the drug delivery device. In at least one embodiment, the needle / trocar retraction can be configured to occur after the end of drug administration, as triggered by, for example, the regulatory mechanism and / or one or more of the status readers as outlined. described in this document.
In yet another embodiment, the drive mechanism may include a status reader configured to read or recognize one or more corresponding status triggers. The status triggers can be gradually separated at the connection, where, during operation of the drive mechanism, the interaction between the status reader and the status triggers transmits a signal to a power and control system to provide feedback to a patient. The status reader can be an optical status reader and the corresponding status triggers are optical status triggers, an electromechanical status reader and the corresponding status triggers are electromechanical status triggers, or a mechanical status reader and status triggers. Corresponding state are mechanical state triggers.
In another embodiment, the present disclosure provides a drug delivery pump with controlled drug delivery. The drug delivery pump having a housing and an assembly platform, on which an activation mechanism, an insertion mechanism, a fluid path connector, a power and control system and a drive mechanism can be mounted. controlled release, said drive mechanism having a drive housing, a piston and a thrust element, wherein the thrust member is initially retained in an energized state and is configured to press on a piston interface surface. The piston is configured to translate substantially axially within a drug container having a piston seal and a cylinder. A joint is connected at one end to the piston and at another end to a cable / gear drum of a management regulating mechanism, where the joint restricts the free expansion of the
141 thrust from its initial energized state and the free axial translation of the piston on which the thrust element presses. The drug container may contain a drug fluid within a drug chamber for administration to a patient. Optionally, a protective sleeve between the push element and the piston interface surface can be used to hide the interior components of the cylinder (namely, the piston and the push element) from view during operation of the drive mechanism. The joint is configured to be released from a cable / gear drum of the administration regulating mechanism to measure the free expansion of the thrust element from its initial energized state and the free axial translation of the piston on which the thrust element presses. .
In another embodiment, the drug delivery device further includes a gear assembly. The gear assembly may include a wire gear connected to a wire / gear drum on which the joint can be wound separately, rotation of the wire / gear drum releases the wire / gear drum joint to measure the free expansion of the thrust element from its initial energized state and free axial translation of the piston on which the thrust element presses. Measurement of binding controls the rate or profile of drug delivery to a patient. The piston can be one or more parts and connects to a distal end of the joint. The cable / gear drum is coupled to a regulating mechanism that controls the rotation of the cable / gear drum and therefore the measurement of piston translation.
In yet another embodiment, the drug delivery device may include a status reader configured to read or recognize one or more corresponding status triggers. The status triggers can be gradually separated at the junction, where, during operation of the drive mechanism, the interaction between the status reader and the status triggers transmits a signal to a power and control system to provide feedback to a patient. The status reader can be an optical status reader and the corresponding status triggers are optical status triggers, an electromechanical status reader and the corresponding status triggers are electromechanical status triggers, or a mechanical status reader and status triggers. Corresponding state are mechanical state triggers.
In another embodiment, the drug delivery device power and control system is configured to receive one or more inputs to measure the release of the joint by the cable / gear drum and thus allow axial translation of the piston by the delivery member. push to translate a piston seal into a cylinder. The one or more inputs may be provided by actuation of the trigger mechanism, a control interface, and / or a remote control mechanism. The power and control system can be configured to
142 receive one or more inputs to adjust the restriction provided by the union and the cable / gear drum in the free axial translation of the piston on which the push element presses to meet a desired drug delivery rate or profile, to change the dose volume for administration to the patient, and / or to otherwise start, stop, or pause operation of the drive mechanism.
The novel embodiments of the present disclosure provide actuation mechanisms that are capable of measuring, providing resistance, or otherwise preventing free axial translation of the plunger seal that is used to force an active ingredient out of a drug container. and, thus, control the speed of administration of active ingredients. The novel control delivery drive mechanisms are further capable of providing the incremental state of drug delivery before, during, and after operation of the device. Throughout this specification, unless otherwise indicated, "comprise", "comprises" and "comprising", or related terms such as "includes" or "consists of", are used inclusive rather than exclusively, such that a stated integer or group of integers can include one or more of other not established integers or groups of integers. As will be further described below, the embodiments of the present disclosure may include one or more additional components that can be considered standard components in the medical device industry. For example, the embodiments may include one or more batteries used to drive the motor, drive mechanisms, and drug delivery devices of the present disclosure. The components, and the embodiments containing such components, are within the contemplation of the present disclosure and should be understood to be within the breadth and scope of the present disclosure.
The present disclosure provides multi-function drive mechanisms for controlled release of active ingredients and drug delivery pumps incorporating such multi-function drive mechanisms. The multi-function actuation mechanisms of the present disclosure allow or initiate various functions, including: (i) controlling the rate of drug delivery by measuring, providing resistance, or otherwise preventing free axial translation of the plunger seal being used to force an active ingredient out of a drug container; (ii) activate a needle insertion mechanism to provide a fluid pathway for drug delivery to a patient; and (iii) connecting a sterile fluid pathway to a drug container to allow fluid flow from the drug container to the needle insertion mechanism for administration to the patient. The driving mechanisms of the present disclosure control the rate of drug administration by measuring, providing resistance or
143 otherwise preventing free axial translation of the plunger seal which is used to force an active ingredient out of a drug container and thus are able to deliver active ingredients at varying rates and / or delivery profiles. Additionally, the driving mechanisms of the present disclosure provide built-in status indication features that provide feedback to the patient before, during, and after drug administration. For example, the patient may provide initial feedback to identify that the system is operational and ready for drug administration. Upon activation, the system can then provide one or more indications of the drug delivery status to the patient. Upon completion of drug administration, the drive mechanism and drug delivery device can provide an end-of-dose indication.
The novel devices of the present disclosure provide drive mechanisms with integrated status indication and drug delivery pumps incorporating such drive mechanisms. Such devices are safe and easy to use, and are aesthetically and ergonomically attractive for self-administration to patients. The devices described in this document incorporate features that make device activation, operation, and locking simple for even untrained patients. The novel devices of the present disclosure provide these desirable features without any of the problems associated with known prior art devices. Certain non-limiting embodiments of the novel drug delivery pumps, drive mechanisms, and their respective components are further described herein with reference to the accompanying figures.
FIGS. 1A-1C show an exemplary drug delivery device according to at least one embodiment of the present disclosure with the top casing removed so that the internal components are visible. The drug delivery device can be used to administer the administration of a drug treatment in a patient's body. As shown in Figs. 69A-69C, the 8000 drug delivery device includes an 8012 pump casing. The 8012 pump casing may include one or more casing subcomponents that can be fixedly connected to facilitate easier manufacturing, assembly, and operation of the delivery device. of drug. For example, the drug delivery device 8000 includes a pump housing 8012 which may include an upper housing and a lower housing (not shown to facilitate visualization of internal components). The drug delivery device may further include an activation mechanism, a status indicator, and a window. The window can be any translucent or transmissive surface through which the operation of the drug delivery device can be visualized. As shown in
144
Fig. 69B, the drug delivery device 8000 further includes an assembly platform 8020, the sterile fluid conduit 8030, drive mechanism 8100 having the drug container 8050, insertion mechanism 8200, fluid path connector 8300 and a power and control system (not shown). One or more of the components of such drug delivery devices may be modular in that it may, for example, be pre-assembled as separate components and configured in place on the mounting platform 8020 of the drug delivery device 8000 during manufacturing.
The pump casing 8012 contains all the components of the device and provides a means of mobile attachment of the device 8000 to the patient's skin. The 8012 pump casing also provides protection to the interior components of the 8000 device against environmental influences. The 8012 pump casing is ergonomically and aesthetically designed in size, shape, and related features to facilitate easy packaging, storage, handling, and use by patients who may be untrained and / or physically handicapped. Furthermore, the external surface of the 8012 pump casing can be used to provide product labeling, safety instructions, and the like. Additionally, as described above, housing 8012 can include certain components, such as one or more status indicators and windows, that can provide operational feedback to the patient.
In at least one embodiment, the drug delivery device 8000 provides an activation mechanism that is displaced by the patient to activate the start command to the power and control system. In a preferred embodiment, the trigger mechanism is a start button that is located through the 8012 pump casing, such as through an opening between the upper casing and the lower casing, and that contacts both directly and indirectly with the power and control system. In at least one embodiment, the start button may be a push button, and in other embodiments, it may be an on / off switch, a switch, or any similar activation feature known in the art. The 8012 pump casing also provides one or more status indicators and windows. In other embodiments, one or more of the trigger mechanism, status indicator, window, and combinations thereof, may be provided in the upper housing or the lower housing such as, for example, on a side visible to the patient when the 8000 drug delivery device is placed on the patient's body. Housing 8012 is described in more detail hereinafter with reference to other components and embodiments of the present disclosure.
The drug delivery device 8000 is configured such that upon activation by a patient by pressing the activation mechanism, the multi-function actuation mechanism is activated to: insert a fluid pathway into the patient; allow,
145 connect or open necessary connections between a drug container, a fluid path, and a sterile fluid line; and forcing the drug fluid stored in the drug container through the fluid path and fluid line for administration to a patient. In at least one embodiment, such administration of drug fluid into a patient is accomplished by the multi-function actuation mechanism in a controlled manner. One or more optional safety mechanisms can be used, for example, to prevent premature activation of the drug delivery device. For example, an optional body sensor (not visible) may be provided in one embodiment as a safety feature to ensure that the power and control system, or trigger mechanism, cannot be connected unless the drug delivery device 8000 is in contact with the patient's body. In such an embodiment, the sensor in the body is located in the lower part of the lower housing where it can contact the patient's body. After movement of the sensor in the body, the activation mechanism is allowed to pulse. Accordingly, in at least one embodiment, the sensor in the body is a mechanical safety mechanism, such as, for example, a mechanical lock, which prevents activation of the drug delivery device 8000 by the activation mechanism. In another embodiment, the sensor in the body can be an electro-mechanical sensor, such as a mechanical lock that sends a signal to the power and control system to allow activation. In still other embodiments, the sensor in the body may be electrically based such as, for example, a capacitive or impedance based sensor that must detect tissue before allowing activation of the power and control system. In at least one embodiment, a sensor in the electrically based body can incorporate a resistor with an impedance of approximately (eg, ± 10%) 1 ΜΩ. These concepts are not mutually exclusive and one or more combinations may be used within the scope of the present disclosure to prevent, for example, premature activation of the drug delivery device. In a preferred embodiment, the drug delivery device 8000 uses one or more mechanical sensors on the bodies. Additional integrated security mechanisms are described herein with reference to other components of the novel drug delivery devices.
XI .A. Power and control system
The power and control system may include a power source, which provides the power for various electrical components within the drug delivery device, one or more feedback mechanisms, a microcontroller, a printed circuit, one or more conductive pads, and one or more interconnections. Other components commonly used in such electrical systems may also be included, as would be appreciated by one of ordinary skill in the art. The one or more mechanisms of
146 Feedback can include, for example, audible alarms such as piezo alarms and / or light indicators such as light emitting diodes (LEDs). The microcontroller can be, for example, a microprocessor. The power and control system controls various interactions of the device with the patient and connects to the 8100 drive mechanism. In one embodiment, the power and control system connects both directly and indirectly to the sensor in the body 24 to identify when the device is in contact with the patient and / or the activation mechanism to identify when the device has been activated. The power and control system can also connect to the 8012 pump casing status indicator, which can be a transmissive or translucent material that allows light transfer, to provide visual feedback to the patient. The power and control system connects to the 8100 drive mechanism through one or more interconnects to transmit status indication, such as activation, drug delivery, and end of dose, to the patient. Such a status indication can be presented to the patient by audible tones, such as through audible alarms, and / or by visual indicators, such as by LEDs. In a preferred embodiment, the control connects between the power and control system and the other components of the drug delivery device do not interact or connect until activated by the patient. This is a desirable safety feature that prevents accidental operation of the drug delivery device and can additionally maintain the energy contained in the power source during storage, transportation, and the like.
The power and control system can be configured to provide several different status indicators to the patient. For example, the power and control system can be configured so that after pressing the sensor into the body and / or activating the mechanism, the power and control system provides a ready-to-start status signal via the status indicator if the Device boot checks do not provide errors. After providing the ready-to-start status signal and, in one embodiment with the optional body sensor, if the sensor in the body contacts the patient's body, the power and control system will drive the 8100 drive mechanism. to begin drug treatment delivery through fluid path connector 8300 and sterile fluid line 8030 (not shown).
Additionally, the power and control system can be configured to identify that the drug delivery device has been removed from its packaging. The power and control system can be mechanically, electronically, or electro-mechanically connected to the package so that when the drug delivery device is removed from the package the power and control system can be activated or turned on for use, or simply allow the power and control system is switched on by the patient. In such an embodiment, without removing
147 the drug delivery device in the packaging, the drug delivery device cannot be activated. This provides an additional safety mechanism for the drug delivery device and for the patient. In at least one embodiment, the drug delivery device or power and control system may be electronically or electro-mechanically connected to the package, for example, such as by one or more interaction sensors from a variety of: effect sensors Hall; giant magnetoresistance (GMR) or magnetic field sensors; optical sensors; capacitive or capacitance change sensors; ultrasonic sensors; and linear path sensors, LVDT, linear resistive, or radiometric linear resistive; and combinations thereof, which are capable of coordinating to transmit a signal between components to identify the location between them. Additionally, or alternatively, the drug delivery device or power and control system may be mechanically connected to the packaging, such as by a bolt-to-groove relationship that activates the system when the bolt is removed (i.e. once the drug delivery device is removed from the packaging).
In a preferred embodiment of the present disclosure, once the power and control system has been activated, the multi-function drive mechanism is started to drive the insertion mechanism 8200 and the fluid path connector 8300, while also The drug fluid is allowed to be forced out of the drug container. During the drug delivery process, the power and control system is configured to provide a dispense status signal via the status indicator. After the drug is administered to the patient's body and after the end of any additional sampling time, to ensure that substantially all of the dose is delivered to the patient, the power and control system can provide an acceptable status signal withdraw via the indicator of State. This can be independently identified by the patient by viewing the drive mechanism and drug dose delivery through the window of the 8012 pump housing. Additionally, the power and control system can be configured to provide one or more warning signals. by means of the status indicator, such as, for example, alerts indicative of failure or operational failure situations.
The power and control system can further be configured to accept various patient inputs to dynamically control 8100 drive mechanisms to meet a desired drug delivery rate or profile. For example, the power and control system may receive inputs, such as full or partial activation, push and / or release of the activation mechanism, to set, start, stop, or otherwise adjust the control of the 8100 drive mechanism. using the power and control system to meet the rate or profile of drug administration
148 wanted. Similarly, the power and control system can be configured to receive such inputs to adjust the drug dose volume; to detect the drive mechanism, fluid line connector and fluid line; and / or to start, stop, or pause the operation of the 8100 drive mechanism. Such inputs may be received directly by the patient by acting on the drug delivery device 8000, such as by use of the trigger mechanism 8014 or a different Control Interface, or the power and control system may be configured to receive such inputs from a remote control device. Additionally or alternatively, such inputs can be pre-programmed.
Other configurations of the power and control system can be used with the novel drug delivery devices of the present disclosure. For example, certain activation delays can be used during drug administration. As mentioned above, a delay optionally included within the system configuration is a sampling time that ensures that substantially all of the drug dose has been delivered before completion of signaling to the patient. Similarly, activation of the device may require a delayed press (i.e., press) of the activation mechanism of the drug delivery device 8000 prior to activation of the drug delivery device. Additionally, the system may include a feature that allows the patient to respond to end-of-dose signals and disable or turn off the drug delivery device. Such a feature may similarly require a delayed press of the activation mechanism, to prevent accidental deactivation of the device. Such features provide desirable security integration and ease of use parameters to drug delivery devices. An additional safety feature can be integrated into the activation mechanism to prevent partial pulsation and thus partial activation of drug delivery devices. For example, the activation mechanism and / or power and control system can be configured such that the device is both fully powered off and fully powered on, to prevent partial activation. Such features are described in more detail hereafter with respect to other aspects of the novel drug delivery devices.
XI.B. Insertion mechanism
Various insertion mechanisms can be used within the drug delivery devices of the present disclosure. The pump-type delivery devices of the present disclosure can be connected in fluid flow communication to a patient or patient, for example, through any suitable hollow tube. A solid drill needle can be used to pierce the patient's skin and place a hollow cannula into the
149 appropriate administration position, with the solid drill needle removed or retracted prior to drug administration to the patient. As stated above, fluid can be introduced into the body through any number of means, including, but not limited to: an automatically inserted needle, cannula, micro-needle array, or infusion set tube. Various mechanisms can also be employed to activate needle insertion in the patient. For example, a push element such as a spring can be employed to provide sufficient force to cause the needle and cannula to pierce the patient's skin. The same spring, an additional spring, or other similar mechanism can be used to retract the patient's needle. In a preferred embodiment, the insertion mechanism can generally be as described in International Patent Application No. PCT / US2012 / 53174, which is included by reference herein in its entirety for all purposes. Such a configuration can be used for insertion of the drug administration route into, or below, the patient's skin (or muscle) in a manner that minimizes pain to the patient. Other known methods for insertion of a fluid pathway may be used and are contemplated within the limits of the present disclosure, including a rigid needle insertion mechanism and / or a rotational needle insertion mechanism as described herein. divulgation.
In at least one embodiment, the insert mechanism 8200 includes an insert mechanism housing having one or more locking windows, and a base for connection to the assembly platform and / or pump housing (as shown in Fig. 69B and Fig. 69C). The connection of the base to the 8020 assembly platform can be, for example, such that the bottom of the base is allowed to pass through a hole in the assembly platform to allow direct contact of the base with the patient's body. In such configurations, the bottom of the base may include a sealing membrane that is mobile prior to use of the 8000 drug delivery device. The insertion mechanism may further include one or more insertion push elements, a needle, a retraction push element, a cannula, and a manifold. The manifold can connect to the 8030 sterile fluid line to allow fluid flow through the manifold, cannula, and into the patient's body during drug administration.
As used herein, "needle" is intended to refer to a variety of needles including, but not limited to, conventional hollow needles, such as a rigid hollow steel needle and solid core needles more commonly called "trocars" . In a preferred embodiment, the needle is a 27 gauge solid core trocar and in other embodiments the needle may be any needle of adequate size to insert the cannula for the type of drug and drug delivery (eg, subcutaneous, intramuscular , intradermal, etc.) planned. A sterile boot can be used inside the
150 needle insertion mechanism. The sterile boot is a collapsible sterile membrane that is in fixed connection at a proximal end with the manifold and at a distal end with the base. In at least one embodiment, the sterile boot is held in a fixed connection at a distal end between the base and the insert mechanism housing. The base includes a base opening through which the needle and cannula can pass through during operation of the insertion mechanism, as will be further described below. The sterility of the cannula and needle are maintained by their Initial positioning within the sterile portions of the insertion mechanism. Specifically, as described above, the needle and cannula are kept in the sterile environment of the collector and the sterile boot. The base base opening can also be closed from non-sterile environments, such as by, for example, a (non-visible) sealing membrane.
According to at least one embodiment of the present disclosure, the insertion mechanism is initially locked in a ready-to-use state by locking bolt (s) that are initially positioned within locking windows of the insertion mechanism housing. In this initial configuration, the insertion push member and the retract push member are each retained in their compressed energized states. Displacement of the locking bolt (s), by one or more methods such as drag, push, slide and / or rotation, allows the push insert element to decompress from its initial compressed energized state. This decompression of the insert thrust element actuates the needle and optionally the cannula in the patient's body. At the end of the insertion stage or at the end of drug administration (as triggered by the multi-function actuation mechanism), the retraction thrust member is allowed to expand in the proximal direction from its initial energized state. This axial expansion in the proximal direction of the retraction thrust member retracts the needle. If an inserted needle / trocar and cannula configuration is used, retraction of the needle may occur while maintaining the cannula in fluid communication with the patient's body. Accordingly, the insertion mechanism can be used to insert a needle and cannula into the patient, and subsequently retract the needle while retaining the cannula in position for drug delivery to the patient's body.
XI.C. Fluid Path Connector
Various fluid path connectors can be used within the embodiments of the present disclosure. Generally, a suitable fluid path connector includes a sterile fluid conduit, a piercing element, and a sterile sleeve attached to a drug container, or an integrated sliding pierceable seal within a drug container. The fluid path connector may further include one or more flow restrictors. Upon proper activation of the 8000 device, the 8300 fluid path connector is allowed
151 connect the sterile fluid line 8030 to the drug container of the 8100 drive mechanism. Such connection may be facilitated by a piercing element, such as a needle, which penetrates a pierceable seal of the drug container of the 8100 drive mechanism. Sterility of this connection can be maintained by making the connection within a flexible sterile sleeve. Upon substantially simultaneous activation of the insertion mechanism, the fluid pathway between the drug container and the insertion mechanism is completed to allow delivery of drug into the patient's body. In such an embodiment, the fluid path connector can be substantially similar to that described in International Patent Application No. PCT / US2012 / 054861, which is included by reference herein in its entirety for all purposes. In such an embodiment, a compressible sterile sleeve can be fixedly attached between the drug container lid and the connection hub of the fluid path connector. The piercing element can reside within the sterile sleeve until a connection between the fluid connection path and the drug container is desired. The sterile sleeve can be sterilized to ensure sterility of the piercing element and fluid path prior to activation.
Alternatively, the fluid path connector can be integrated into a drug container as described in International Patent Applications No. PCT / US2013 / 030478 or No. PCT / US2014 / 052329, for example, which are included by Reference in this document in its entirety for all purposes. In accordance with such an embodiment, a drug container may have a drug chamber within a cylinder between a pierceable seal and a plunger seal. A drug fluid is contained in the drug chamber. Upon activation of the device by the patient, a drive mechanism exerts a force on a plunger seal contained in the drug container. As the plunger seal exerts a force on the drug fluid and any air / gas voids or bubbles, a combination of pneumatic and hydraulic compression of air / gas and drug fluid is formed and the force is transmitted to the The sliding perforable seal. The pierceable EI seal is caused to slide into the cap, causing it to be pierced by the piercing element retained within the integrated sterile fluid path connector. Accordingly, the integrated sterile fluid path connector is connected (i.e., the fluid path is opened) by the combination of pneumatic / hydraulic force of air / gas and drug fluid within the drug chamber created by the activation of a drive mechanism. Once the integrated sterile fluid path connector has been connected or opened, the drug fluid is allowed to flow from the drug container, through the integrated sterile fluid path connector, the sterile fluid line, and the mechanism insertion, and into the patient's body for drug administration. In at least one embodiment, the fluid flows through only a manifold and a cannula and / or needle of the insertion mechanism, thus maintaining sterility
152 of the fluid pathway before and during drug administration.
In a preferred embodiment, the sterile fluid path connector is initiated by movement of the needle insertion mechanism, which itself is initiated by the multi-function actuation mechanism. Additionally or alternatively, the sterile fluid path connector is initiated by movement directly from the multi-function drive mechanism. For example, the multi-function drive mechanism may include a rotational gear, such as the star gear described in detail herein, which acts simultaneously or sequentially to control the rate of drug delivery, to drive the insertion mechanism. needle, and / or start the sterile fluid path connector. In a particular embodiment, shown in Figs. 69A-69C, the multi-function drive mechanism performs all of these stages substantially simultaneously. The multi-function drive mechanism rotates a gear that acts behind various other components. The gear acts on a gear assembly to control the rate of drug delivery, while a needle insertion mechanism is also contacted to introduce a fluid pathway into the patient. As the needle insertion mechanism starts, the sterile fluid connection is made to allow the flow of drug fluids from the drug container, through the fluid passage, into the needle insertion mechanism, for the delivery to the patient as the gear and gear assembly of the multi-function drive mechanism control the rate of drug delivery.
Regardless of the fluid path connector used by the drug delivery device, the drug delivery device is capable of delivering a variety of drugs with different viscosities and volumes. The drug delivery device is capable of delivering a drug at a controlled flow rate (rate) and / or a specified volume. In one embodiment, the drug delivery process is controlled by one or more flow restrictors within the fluid path connector and / or the sterile fluid line. In other embodiments, other flow rates may be provided by varying the geometry of the fluid flow path or delivery line, varying the rate at which a component of the drive mechanism advances into the drug container to dispense the drug therein, or combinations thereof. Still more details about the fluid path connector 8300 and the sterile fluid line 8030 are provided hereafter in later sections referring to other embodiments.
XI.D. Multi-function drive mechanism
The multi-function drive mechanisms of the present disclosure allow or initiate various functions, including: (i) controlling the rate of administration of
153 drug by measuring, providing resistance, or otherwise preventing free axial translation of the plunger seal used to force an active ingredient out of a drug container; (I) activate a needle insertion mechanism to provide a fluid path for drug administration to a patient; and (iii) connecting a sterile fluid pathway to a drug container to allow fluid flow from the drug container to the needle insertion mechanism for administration to the patient. With reference to the embodiments shown in Figs. 70A-70D and 71A-71D, the 8100 multi-function drive mechanism includes a push button 8101, a gear assembly 8110 including a main gear 8102, a drive housing 8130, and an 8050 drug container having an 8052 cap, a perforable seal (not visible), an 8058 cylinder and an 8060 piston seal. The main gear 8102 may be, for example, a star gear arranged to contact multiple secondary gears or the surface of the gear. A drug chamber 8021, located within cylinder 8058 between the pierceable seal and plunger seal 8060, may contain a drug fluid for delivery through the insertion mechanism and drug delivery device into the patient's body. The gaskets described herein can comprise various materials, but in a preferred embodiment, comprise one or more elastomers or rubbers. The drive mechanism 8100 may further contain one or more drive push elements, one or more release mechanisms, and one or more guides, as further described herein. The drive mechanism components serve to force a fluid out of the drug container through the pierceable seal, or preferably through the piercing element of the fluid line connector, for delivery through the line connector. of fluid, sterile fluid conduit and insertion mechanism in the patient's body.
In a particular embodiment, the drive mechanism 8100 employs one or more compression springs as the push element (s). Upon activation of the drug delivery device by the patient, the power and control system may be actuated to directly or indirectly release the compression springs (s) from an energized state. Upon release, the compression springs (s) can press on and act on the plunger seal to force fluid drug out of the drug container. The compression spring can press against and act on a piston which, in turn, acts on the plunger seal to force fluid drug out of the drug container. The fluid path connector can be connected through the pierceable seal before, simultaneously with, or after activation of the drive mechanism to allow fluid flow from the drug container, through the fluid path connector, line of sterile fluid and insertion mechanism, and into the patient's body for drug administration. In at least one embodiment, the fluid flows through only one manifold and one cannula of the insertion mechanism,
154 thus maintaining the sterility of the fluid pathway before and during drug administration. Such components and their functions are described in more detail herein.
Referring now to the embodiment of the multi-function drive mechanism shown in Figs. 70A-70D and 70A-70D, the 8100 multi-function drive mechanism includes a push button 8101, a gear assembly 8110 including a main gear 8102, a drive housing 8130 and an 8050 drug container having an 8052 cap, a perforable seal (not visible), an 8058 cylinder and an 8060 piston seal. The main gear 8102 may be, for example, a star gear arranged to contact multiple secondary gears or the surface of the gear. A drug chamber 8021, located within cylinder 8058 between the pierceable seal and plunger seal 8060, may contain a drug fluid for delivery through the Insertion mechanism and drug delivery device into the patient's body. Within the drive housing 8130, between the drug container 8050 and the proximal end of the housing 8130, are compressed one or more drive push members 8122 and a piston 8110, wherein the drive push members 8122 are configured to press on an interface surface 8110C of piston 8110, as further described herein. Optionally, a protective sleeve (not shown) can be used between the drive push members 8122 and the interface surface 8110C of the piston 8110 to, for example, promote a more even distribution of force from the drive push member 8122 to the piston 8110 , preventing the collapse of the actuating push elements 8122, and / or hiding the pushing elements 8122 from the patient's view. The interface surface 8110C of piston 8110 is caused to lie substantially adjacent to, or in contact with, a proximal end of gasket 8060. Although the embodiments shown in Figs. 70A-70D and 71A-71D show a unique push element, it is also contemplated that one or more push elements arranged to operate in parallel can be used.
As shown in FIG. 70D and FIG. 71D, the piston 8110 may comprise two components 8110A and 8110B and have an interface surface 8110C for contacting the piston seal. A joint, tape, rope, or other retaining strip (referred to herein as "joint" 8525) may be connected at one end with piston 8110A, 8110B. For example, joint 8525 can be connected to piston 8110A, 8110B by retention between the two components of piston 8110A, 8110B when assembled. The 8525 junction connects at another end to an 8520 cable / gear drum of an 8500 management control mechanism. Through the use of the 8520 cable / gear drum connected to one end of the 8525 joint, and the 8525 joint connected to the other end to the piston 8110A, 8110B, the regulation mechanism 8500 works by controlling, measuring, providing resistance
155 or otherwise preventing free axial translation of the piston 8110A, 8110B and the piston seal 8060 used to force an active ingredient out of a drug container 8050. Accordingly, the regulating mechanism 8500 is a portion of the appearance of the Gear assembly 8116 of the multi-function actuation mechanism, which together serve to control the rate or profile of drug delivery to the patient.
As shown in Figs. 70A-70D and 71A-71D, and in isolation in Figs. 72 and 73A-73B, in the embodiments of the present disclosure, the regulating mechanism 8500 is the gear assembly actuated by a push button 8101 of the 8100 multi-function actuating mechanism. The regulating mechanism delays or limits the distribution of the joint 8525, only allowing it to advance at a regulated or desired speed. This restricts movement of piston 8110 within cylinder 8058, which is pushed by one or more push members 8122, thus controlling movement of piston seal 8060 and delivery of drug contained in chamber 8021. As the plunger seal 8060 advances into the drug container 8050, the active ingredient is dispensed through the sterile line connection 8300, conduit 8030, insertion mechanism 8200 and into the patient's body for drug delivery. Push button 8101 can be various power / motion sources including, for example, a solenoid, a stage motor, or a rotational action motor. In a particular embodiment, the push button 8101 is a rotational stage motor with a slot corresponding to the gear teeth of the star / main gear 8102. Typically, such a rotational stage motor may be referred to as a 'Pac-Man' motor . In at least one embodiment, the Pac-Man engine has a gear interface within which one or more teeth of the main gear may partially reside during system operation. This is more clearly visible in Figs. 73A-73B. When the 8101A gear interface of the Pac-Man 8101 motor is in alignment with a tooth 8102A of the 8102 main gear, the rotational movement of the 8101 Pac-Man motor causes the movement of the 8102 main gear gear interface. When the PacMan 8101 motor is between gear teeth of the main gear, it can act as a resistor for, for example, reverse rotation or unwinding of the 8116 gear assembly. Additional detail on the 8116 gear assembly, 8500 timing mechanism and 8100 multi-function drive mechanism are provided herein.
In a particular embodiment shown in Figs. 73A-73B, the regulating element 8500 further includes one or more gears 8511, 8512, 8513, 8514, of a gear assembly 8516. One or more of the gears 8511, 8512, 8513, 8514 may be, for example, gears Compounds that have a small diameter gear attached at a shared central point with a larger diameter gear. Gear 8513 can
156 be rotationally coupled to the gear / cable drum 8520, for example by a keyed shaft, thereby coupling rotation of the gear assembly 8516 to the gear / cable drum 8520. The 8512 compound gear engages the 8513 small diameter gear so that The rotational motion of the 8512B composite gear aspect is carried by the connection of the gears (such as by the connection of corresponding gear teeth) to the gear 8513. The 8512A composite gear aspect, whose rotation is coupled to the 8512B aspect gear, is caused to rotate by the action of the 8102B composite gear aspect of the 8102 main / star gear. The 8102B composite gear aspect, whose rotation is caused to mates to 8102 main / star gear, rotate through interaction between 8102A main / star gear and 8101A push button interface 8101A. Thus, rotation of the main / star gear 8102 is conveyed to the cable / gear drum 8520. Accordingly, the rotation of the gear assembly 8516 initiated by the push button 8101 can be coupled to the cable / gear drum 8520 (ie, to through gear assembly 8516), thus controlling the distribution of joint 8525, and the speed of movement of plunger seal 8060 within cylinder 8058 to force fluid out of drug chamber 8021. The rotational movement of the cable / gear drum 8520, and thus the axial translation of the piston 8110 and the piston seal 8060, are measured, limited, or otherwise prevented by free axial translation by other components of the regulation element 8500, as described in this document. As described above, push button 8101 may be a number of known power / motion sources including, for example, a motor (for example, a DC motor, AC motor, or stage motor) or a solenoid (for example, linear solenoid, rotary solenoid).
In particular, the regulatory mechanisms 8500 of the present disclosure do not drive the delivery of fluid substances from the drug chamber 8021. The delivery of fluid substances from the drug chamber 8021 is caused by the expansion of the push member 8122 from its state initial energized acting on piston 8110A, 8110B and piston seal 8060. Regulating mechanisms 8500 operate in place providing resistance to free movement of piston 8110A, 8110B and plunger seal 8060 as they are pushed by expansion of push member 8122 from its initial energized state. The 8500 regulatory mechanism does not drive administration, but only controls the movement of administration. The joint otherwise limits or restricts the movement of piston 8110 and piston seal 8060, but does not apply force for administration. According to a preferred embodiment, the controlled release actuation mechanisms and drug delivery devices of the present disclosure include a regulating mechanism indirectly or directly connected with a joint that measures axial translation of the piston 8110A, 8110B and the piston seal 8060,
157 which are being driven to be axially translated by the thrust element 8122. The rate of drug administration as controlled by the regulatory mechanism can be determined by; selecting the gear ratio of the 8516 gear assembly; main / star gear selection 8102; 8520 Gear / Winding Drum Diameter Selection; using 8101 electromechanical push button to control rotational speed of main / star gear 8102; or any other method known to a person skilled in the art. Using the electromechanical push button 8101, the rotation speed of the main / star gear 8102 may be possible to configure a drug delivery device to provide a variable dose rate (i.e., the rate of drug delivery is varied during a treatment ).
In another embodiment, the drug delivery device power and control system is configured to receive one or more inputs to measure the release of the joint 8525 by the cable / gear drum 8520 and thus allow axial translation of the piston 8110 by the thrust element 8122 to translate a piston seal 8060 into a cylinder 8058. The one or more inputs may be provided by actuation of the trigger mechanism, a control interface, and / or a remote control mechanism. The power and control system can be configured to receive one or more inputs to adjust the limitation provided by joint 8525 and gear / cable drum 8520 to the free axial translation of piston 8110 on which thrust element 8122 presses to meet a desired drug delivery rate or profile, to change the dose volume for administration to the patient, and / or to start, otherwise stop or pause the operation of the drive mechanism.
The components of the drive mechanism 8100, upon activation, can be used to drive axial translation in the distal direction of the plunger seal 8060 of the drug container 8050. Optionally, the drive mechanism 8100 may include one or more compliance features. that allow for additional axial translation of the 8060 plunger seal to, for example, ensure that the entire dose of drug has been delivered substantially to the patient. For example, the plunger seal 8060, itself, may have some compressibility that allows for a drug fluid compliance effort from the drug container.
The novel controlled release drive mechanisms of the present disclosure can optionally integrate status indication into drug dose delivery. Using one or more status triggers and a corresponding status reader, the status of the drive mechanism before, during, and after operation can be transmitted to the power and control system to provide feedback to the patient. Such feedback can be tactile, visual and / or auditory, as
158 described above, and may be redundant so that more than one signal or type of feedback is provided to the patient during use of the device. For example, the patient may provide initial feedback to identify that the system is operational and ready for drug administration. Upon activation, the system can then provide one or more indications of the drug delivery status to the patient. Upon completion of drug administration, the drug delivery mechanism and drive mechanism can provide an end-of-dose indication. As the end of dose indication is attached to the piston reaching the end of its axial translation, the actuation mechanism and drug delivery device provide a true end of dose indication to the patient.
Junction 8525 may have one or more status triggers, such as electrical contacts, optical markings, or electromechanical bolts or gaps, that are capable of contacting or being recognized by a status reader. In at least one embodiment, an end of dose status indication may be provided to the patient once the status reader contacts or recognizes the end status trigger positioned at junction 8525 that would contact the status reader. been at the end of the axial travel of piston 8110A, 8110B and plunger 8060 within cylinder 8058 of drug container 8050. The status reader can be, for example, an electrical commutation reader to contact the corresponding electrical contacts, an optical reader to recognize the corresponding optical marks, or a mechanical or electromechanical reader configured to contact corresponding bolts, holes, or the like. in the union. Status triggers may be positioned along junction 8525 to be read or recognized at positions that correspond to the beginning and end of drug delivery, in addition to desired increments during drug delivery. As the drug delivery device is activated and drug delivery is started by releasing push member 8122 and the resulting force applied to piston 8110A, 8110B and plunger seal 8060, the rate or profile of drug delivery the patient is controlled by the regulation mechanism 8500, the 8516 gear assembly and the 8520 cable / gear drum that looses the 8525 joint and allows expansion of the thrust element 8122 and axial translation of the piston 8110A, 8110B and the 8060 piston seal. As this occurs, the junction status triggers 8525 are contacted or recognized by the status reader and the status of the drive mechanism before, during, and after which the operation can be transmitted to the power and control to provide patient feedback. Depending on the number of status triggers located on junction 8525, the frequency of the incremental status indication can be varied as desired. As described above, a variety of
159 status readers depending on the status triggers used by the system.
In a preferred embodiment, the status reader can apply a tension force to junction 8525. When the system reaches the end of dose, junction 8525 is loosened and the status reader 8544 is allowed to rotate around a fulcrum. . This rotation can operate an electrical or electromechanical switch, for example a switch, that signals loosening at junction 8525 to the power and control system. Additionally, a gear 8511 in gear assembly 8516 can act as an encoder along with a sensor. The sensor / encoder combination is used to provide feedback on the rotation of the gear assembly, which in turn can be calibrated to the position of the 8110 piston when there is no loosening at the 8525 joint. Together, the status reader and sensor / encoder can provide positional feedback, end-of-dose signal, and error indication, such as an occlusion, with loosening being observed at junction 8525 before reaching the expected number of motor rotations as counted. by the sensor / encoder.
Referring again to Figs. 70A-70D and 71A-71D, in addition to controlling the rate of drug delivery by measuring, providing resistance, or otherwise preventing free axial translation of the plunger seal used to force an active ingredient out of a drug container ( thus administering active ingredients at variable speeds and / or administration profiles); The multi-function actuation mechanisms of the present disclosure can simultaneously or sequentially perform the steps of: activating a needle insertion mechanism to provide a fluid pathway for drug delivery to a patient; and connecting a sterile fluid pathway to a drug container to allow fluid flow from the drug container to the needle insertion mechanism for administration to the patient. In at least one embodiment, as shown in Figs. 70A-70D and 71A-71D, initial movement by push button 8101 of 8100 multifunction drive mechanism results in rotation of 8102 main / star gear. 8102 main / star gear is shown as a compound gear with 8102A and 8102B aspects. (see Fig. 72). In one way, star / main gear 8102 transports motion to regulating mechanism 8500 through gear assembly 8516. In other way, star / core gear 8102 transports motion to needle insertion mechanism 8200 through of gear 8112. As gear 8112 rotates through main / star gear 8102, gear 8112 engages needle insertion mechanism 8200 to initiate fluid path connector on the patient, as described in detail above. In a particular embodiment, the needle insertion mechanism 8200 is a rotational needle insertion mechanism. Accordingly, gear 8112 is configured to connect a corresponding gear surface 8208 of needle insertion mechanism 8200. Rotation of gear 8112 results in mechanism rotation.
160 insertion needle 8200 through gear interaction between gear 8112 of drive mechanism 8100 and corresponding gear surface 8208 of needle insertion mechanism 8200. Once proper rotation of needle insertion mechanism 8200 occurs , for example the rotation along the 'R' axis shown in Fig. 70B-70C, the needle insertion mechanism can be initiated to create the fluid path connector in the patient, as described in detail above.
As shown in Figs. 70A-70D and 71A-71D, rotation of the needle insertion mechanism 8200 can also thereby produce a connection of a sterile fluid path to a drug container to allow fluid flow from the drug container to the insertion mechanism. needle for administration to the patient. The ramp appearance 8222 of the needle insertion mechanism 8200 causes it to press on a movable connection hub 322 of the 8300 sterile fluid path connector. As the needle insertion mechanism 8200 is rotated by the multi-function drive mechanism 8100, the ramp aspect 8222 of the needle insertion mechanism 8200 presses on and transports the movable connection hub 322 from the pathway connector. 8300 sterile fluid to facilitate a fluid connection inside. Such translation may occur, for example, in the direction of the hollow arrow along the 'C' axis shown in Figs. 70B and 71B. In at least one embodiment, the needle insertion mechanism 8200 can be configured such that a particular degree of rotation about the rotational axis 'R' (shown in Figs. 70B-70C) allows the needle / trocar to retract as have detailed above. Additionally or alternatively, such needle / trocar retraction can be configured to occur on an activity of the patient or on the movement or function of another component of the drug delivery device. In at least one embodiment, the needle / trocar retraction can be configured to occur upon administration of the drug end, as triggered by, for example, the regulatory mechanism 8500 and / or one or more of the status readers such as described above. During these stages of operation, delivery of fluid substances from drug chamber 8021 can be initiated, continued, and / or completed by expansion of thrust member 8122 from its initial energized state acting on piston 8110A, 8110B, and plunger 8060. As described above, regulating mechanisms 8500 operate by providing resistance to free movement of piston 8110A, 8110B and piston seal 8060 as they are pushed by expansion of push member 8122 from its initial energized state. The 8500 regulatory mechanism does not drive administration, but only controls the movement of administration. The joint otherwise limits or restricts the movement of piston 8110 and piston seal 8060, but does not apply force for administration. This is visible through the progression of the components shown in Figs. 70A-70D and 71A-71D. 8110A piston movement,
161 8110Β and plunger seal 8060 as they are pushed by the expansion of the thrust member 8122 from its initial energized state shown in the direction of the solid arrow along axis' A 'from the proximal or first position' P 'to the distal or second' D 'position, as shown in the transition of Figs. 70A-70D and 71A-71D.
Additional aspects of the novel drive mechanism will be described with reference to Fig. 72 and Figs. 73A-73B. Fig. 4 shows a perspective view of the multi-function actuation mechanism, according to at least a first embodiment, during its initial locking stage. Initially, joint 8525 can retain push member 8122 in an initial energized position within piston 8110A, 8110B. Directly or indirectly, upon activation of the device by the patient, the multi-function 8100 actuation mechanism can be activated to allow the thrust element to impart a force to the piston 8110 and thus to the joint 8525. This force on the Joint 8525 confers a couple of forces on winding drum 8520 that causes gear assembly 8516 and adjusting mechanism 8500 to start moving. As shown in Fig. 73A, piston 8110 and thrust member 8122 are both initially in a compressed energized state beyond piston seal 8060. Thrust member 8122 can be maintained in this state until activation of the device between internal characteristics of the 8130 drive and 8110C interface surface of 8110A, 8110B piston. As the drug delivery device 8000 is activated and the drive mechanism 8100 is triggered to operate, the push member 8122 is allowed to expand (i.e., decompress) axially in the distal direction (i.e., in the solid arrow direction shown in Figs. 70A-70D and Figs. 71A-71D). Such expansion causes thrust member 8122 to act on and distally translate interface surface 8110C and piston 8110, thereby distally moving piston seal 8060 to push drug fluid out of drug chamber 8021 of cylinder 8058. In at least one embodiment, an end-of-dose status indication may be provided to the patient once the status reader contacts or recognizes a status trigger positioned on junction 8525 to substantially correspond to the end of axial travel of piston 8110A, 8110B and plunger seal 8060 inside cylinder 8058 of drug container 8050. Status triggers may be positioned along junction 8525 at various increments, such as increments corresponding to a certain volume measurement, to provide incremental status indication to the patient. In at least one embodiment, the status reader is an optical status reader configured to recognize the corresponding optical status triggers at the junction. As would be understood by a person skilled in the art, such optical state triggers can be marks that are recognizable by the optical state reader. In another embodiment, the status reader is a mechanical or electromechanical reader
162 configured to physically contact corresponding bolts, holes, or the like on the joint. Electrical contacts on the junction could similarly be used as status indicators that contact or are otherwise recognized by the corresponding electrical status reader. Status triggers may be positioned along junction 8525 to be read or recognized at positions that correspond to the beginning and end of drug delivery, in addition to desired increments during drug delivery. As shown, joint 8525 passes substantially axially through drive mechanism housing 8130, thrust member 8122 and connects to piston 8110A, 8110B to restrict axial translation of piston 8110A, 8110B and piston seal 8060 residing adjacent to it.
The novel embodiments of the present disclosure can be used to measure, restrict, or otherwise prevent free rotational movement of winding drum 8520 and thus axial translation of components of the 8100 controlled release drive mechanism. Accordingly, the Regulating Mechanism 8500 only controls movement of the actuating mechanism, but does not apply force for drug delivery. One or more additional thrust elements 8122, such as compression springs, may be used to drive or assist in actuation of the piston 8110. For example, a compression spring within the drive housing 8130 may be used for this purpose. Regulating mechanism 8500 only controls, measures, or regulates such action. The controlled release drive mechanisms and / or drug delivery devices of the present disclosure may further permit a compliance effort to ensure that substantially all of the active ingredient has been removed from drug chamber 8021. Plunger Seal 8060 By itself, it may have some compressibility that allows a compliance effort of the drug fluid from the drug container. For example, when using a bulged plunger seal, that is, a plunger seal that is deformable from an initial state, the plunger seal may be caused to deform or "bulge" to provide a compliance effort of the drug fluid. of the drug container. Additionally or alternatively, an electromechanical status switch and assembly interconnect may be used to contact, connect, or otherwise allow a transmission to the power and control system to signal the end of dose to the patient. This configuration also allows the true indication of end of dose to the patient.
In at least one embodiment, incremental status indication can be provided to the patient by reading or recognizing the rotational motion of one or more gears in gear assembly 8516. As gear assembly 8516 rotates, a status reader can read or recognize one or more corresponding status triggers on one of the gears in the gear assembly to provide
163 Incremental status indication before, during, and after operation of the variable speed controlled release drive mechanism. Various status readers can be used within the embodiments of the present disclosure. For example, the drive mechanism may use a mechanical status reader that is physically contacted by gear teeth on one of the gears in the gear assembly. As the status reader is contacted by the status trigger (s), which in this exemplary embodiment may be the gear teeth of one of the gears (or holes, bolts, bosses, marks, electrical contacts or the like, on the gear), the status reader measures the rotational position of the gear and transmits a signal to the power and control system for status indication to the patient. Additionally or alternatively, the drive mechanism may use an optical status reader. The optical status reader can be, for example, a beam of light that is capable of recognizing movement and transmitting a signal to the power and control system. For example, the drive mechanism may use an optical status reader that is configured to recognize movement of the gear teeth of one of the gears in the gear assembly (or holes, bolts, bosses, marks, electrical contacts, or the like) , on the gear). Similarly, the status reader can be an electrical switch configured to recognize electrical contacts in the gear. In either of these embodiments, the sensor can then be used to transmit a signal to the power and control system to provide feedback to the patient.
As would be appreciated by one of ordinary skill in the art, the corresponding optical status readers and triggers, corresponding electromechanical status readers and triggers, and / or corresponding mechanical status readers and triggers can all be used by the embodiments of the present disclosure to provide incremental status indication to the patient. Although the drive mechanisms of the present disclosure are described with reference to the gear assembly and regulating mechanisms shown in the figures, a variety of configurations may be acceptable and capable of being employed within the embodiments of the present disclosure, as Would be easily appreciated by a person skilled in the art. Accordingly, the embodiments of the present disclosure are not limited to the specific gear assembly and adjusting mechanism described herein, which is provided as an exemplary embodiment of such mechanisms for use within the release drive mechanisms. controlled and drug delivery pumps.
The assembly and / or manufacturing of the 8100 controlled release drive mechanism, the 8000 drug delivery drug delivery device, or any of the individual components can utilize various materials and
164 known methodologies in the field. For example, various known cleaning fluids such as isopropyl alcohol and hexane can be used to clean components and / or devices. Similarly, various known adhesives or glues can be employed in the manufacturing process. Additionally, known siliconization and / or lubrication fluids and processes can be employed during the manufacture of the novel components and devices. In addition, known sterilization processes can be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
The drive mechanism can be assembled in various methodologies. In an assembly method, the 8050 drug container can first be assembled and filled with a fluid for administration to the patient. Drug container 8050 includes a cap 8052, a pierceable seal 8056, a cylinder 8058, and a plunger seal 8060. Pierceable seal 8056 can be fixedly connected between cap 8052 and cylinder 8058, at a distal end of cylinder 8058 . Cylinder 8058 can be filled with a drug fluid through the open proximal end prior to insertion of plunger seal 8060 from the proximal end of cylinder 8058. An optional connection assembly 854 can be mounted on a distal end of pierceable seal 8056. Connection assembly 854 can guide the insertion of the piercing element of the fluid path connector into cylinder 8058 of drug container 8050. Drug container 8050 can then be mounted on a distal end of drive housing 8130.
One or more actuating push elements 8122 can be inserted into a distal end of the 8130 drive housing. Optionally, a protective sleeve 8140 can be inserted into a distal end of the 8130 drive housing to substantially cover the push 8122 element. A piston may be inserted into the distal end of the drive housing 8130 such that it resides at least partially within a passage through axially of the thrust member 8122 and the thrust member 8122 is allowed to contact a piston infeed surface 8110C piston 8110A, 8110B at the distal end of push element 8122. An optional protective sleeve 8140 can be used to enclose thrust member 8122 and contact the piston bottom surface 8110C of piston 8110A, 8110B. The piston 8110A, 8110B and the drive push element 8122, and the optional protective sleeve 8140, can be compressed into the drive housing 8130. Such an assembly positions the actuating thrust member 8122 in an initial compressed energized state, and preferably places a piston inferred surface 8110C in contact with the proximal surface of piston seal 8060 within the proximal end of cylinder 8058. The piston, piston thrust element, contact sleeve, and optional components can be compressed and locked in the ready-to-operate state within the 8130 drive housing prior to attachment or mounting of the
165 Drug container 8050. Junction 8525 is pre-connected to the proximal end of piston 8110A, 8110B and passes through the axial opening of pusher element 8122 and drive mechanism 8130, and is then wound through the interior of the Drug delivery device with the other end of junction 8525 wrapped around cable / gear drum 8520 of regulating mechanism 8500.
A fluid line connector, and specifically a sterile sleeve of the fluid line connector, can be connected to the cap and / or pierceable seal of the drug container. A fluid line can be connected to the other end of the fluid path connector that is itself connected to the insertion mechanism so that the fluid path, when opened, connected, or otherwise enabled, runs directly from the drug container , fluid path connector, fluid line, insertion mechanism, and through the cannula for drug delivery into a patient's body. The components that make up the fluid flow path are now assembled. These components can be sterilized, by various known methods, and then mounted both fixedly and movably on an assembly platform or housing of the drug delivery device, as shown in Fig. 69B.
Certain optional standard components or variations of the 8100 drive mechanism or 8000 drug delivery device are contemplated as long as they remain within the scope and scope of the present disclosure. For example, embodiments may include one or more batteries used to power a motor or solenoid, drive mechanisms, and drug delivery devices of the present disclosure. A variety of batteries known in the art can be used for this purpose. Additionally, upper or lower housings may optionally contain one or more transparent or translucent windows 18 to allow the patient to view the operation of the drug delivery device 8000 or verify that the drug dose has been completed. Similarly, the drug delivery device 8000 may contain an adhesive patch 8026 and a patch liner 8028 on the underside of the housing 8012. The adhesive patch 8026 can be used to adhere the drug delivery device 8000 to the patient's body to administration of the drug dose. As would be readily understood by one of ordinary skill in the art, adhesive patch 8026 may have an adhesive surface for adhesion of the drug delivery device to the patient's body. The adhesive surface of the adhesive patch 8026 may initially be covered by a non-adhesive patch liner 8028, which is removed from the adhesive patch 8026 prior to the placement of the drug delivery device 8000 in contact with the patient's body. Removal of the patch liner 8028 can furthermore remove the sealing membrane 254 from the insertion mechanism 8200, opening the
166
Insertion into the patient's body for drug administration (as shown in Fig. 69C). In some embodiments, removal of the patch liner 8028 may also awaken the on-board electronics (eg, the 2400 power and control system) by supplying it with electricity from an on-board battery.
Similarly, one or more of the components of the 8100 controlled release drive mechanism and 8000 drug delivery device can be modified, as long as they functionally remain within the scope and scope of the present disclosure. For example, as described above, although the 8000 drug delivery device housing is shown as two separate components, the upper housing 8012A and the lower housing 8012B, these components may be a single unified component. As discussed above, a glue, adhesive, or other known materials or methods can be used to attach one or more components of the controlled release drive mechanism and / or drug delivery device to each other. Alternatively, one or more components of the controlled release drive mechanism and / or drug delivery device may be a unified component. For example, the top case and the bottom case can be separate components held together by an adhesive or glue, a threaded fit connection, an interference fit, fusion joint, solder, ultrasonic welding, and the like; or the super shell and the bottom shell can be a single unified component. Such standard functional components and variations would be appreciated by one of ordinary skill in the art and are, therefore, within the scope and scope of the present disclosure.
It will be appreciated from the foregoing description that the controlled release drive mechanisms and drug delivery devices disclosed herein provide an efficient and easily operated system for automatic drug delivery from a drug container. The novel embodiments described herein provide drive mechanisms for the controlled release of active ingredients and drug delivery pumps incorporating such controlled release drive mechanisms. The driving mechanisms of the present disclosure control the rate of drug delivery by measuring, providing resistance, or otherwise preventing free axial translation of the plunger seal used to force an active ingredient out of a drug container and, thus, they are capable of administering active ingredients at variable speeds and / or administration profiles. Additionally, the actuation mechanisms of the present disclosure can provide integrated status indication features that provide feedback to the patient before, during, and after drug administration. For example, the patient may provide initial feedback to identify that the
167 system is operational and ready for drug administration. Upon activation, the system can then provide one or more indications of the drug delivery status to the patient. Upon completion of drug administration, the drug delivery mechanism and drive mechanism can provide an end-of-dose indication. The novel controlled release drive mechanisms of the present disclosure can be directly or indirectly activated by the patient. In addition, the novel configurations of the controlled release drive mechanism and drug delivery devices of the present disclosure maintain sterility of the fluid pathway during storage, transport, and through operation of the device. Because the pathway that the drug fluid travels within the device is completely kept in a sterile condition, only these components need to be sterilized during the manufacturing process. Such components include the drug container of the drive mechanism, the fluid path connector, the sterile fluid line, and the insertion mechanism. In at least one embodiment of the present disclosure, the power and control system, the assembly platform, the control arm, the activation mechanism, the housing, and other components of the drug delivery device do not need to be sterilized. This greatly improves the manufacturing capacity of the device and reduces associated assembly costs. Accordingly, the devices of the present disclosure do not require terminal sterilization upon completion of assembly.
Manufacture of a drug delivery device includes the step of attaching both the controlled release drive mechanism and the drug container, either separately or as a combined component, to an assembly platform or housing of the drug delivery device. drug. The manufacturing method further includes attaching the fluid path connector, drug container, and insertion mechanism to the assembly platform or housing. Additional components of the drug delivery device, as described above, including the power and control system, trigger mechanism, and control arm, can be attached, pre-formed, or pre-assembled to the assembly platform or housing . An adhesive patch and patch liner may be attached to the housing surface of the drug delivery device that contacts the patient during operation of the device.
A method of operating the drug delivery device includes the steps of: activating, by a patient, the activation mechanism; move a control arm to operate an insertion mechanism; and actuating a power and control system to activate a controlled release actuation mechanism to actuate the flow of fluids through the drug delivery device according to a controlled drug delivery rate or profile. The method may further include the step of: connecting a
168 optional sensor in the body before activating the trigger mechanism. The method may similarly include the step of: establishing a connection between a fluid path connector with a drug container. In addition, the method of operation may include moving a plunger seal into the release actuation mechanism controlled by the expansion of the push member acting on a piston within a drug container to force a drug to flow through the container. of drug, the fluid path connector, a sterile fluid line and the insertion mechanism for delivery of drug fluid to a patient's body, wherein a regulating mechanism that acts to restrict the distribution of a joint is used to measure the free axial translation of the piston. The method of operation of the drive mechanism and the drug delivery device can be better appreciated with reference to Figs. 70A-70D and Figs. 71A-71D, as described above.
XII. Temperature monitoring system
For some drugs, temperature is an important consideration both during and before administration to the patient. Biological drugs, for example, sometimes require refrigeration or frozen storage before administration to the patient. Although cold temperatures can help prolong the shelf life of the drug, they can cause an increase in the viscosity of the drug. A more viscous drug may take longer to inject and / or require additional injection force. Also, injecting a cold drug can be uncomfortable, and possibly even painful, for some patients. Therefore, a drug that has been stored in a cold state is normally allowed to warm to near room temperature before administration to the patient. This warm-up period can last more than 30 minutes, which can be inconvenient for the patient and consequently have an adverse impact on patient compliance rates.
The drug delivery devices of the present disclosure can be configured to include a temperature control system to monitor and / or control the temperature of the drug within the device. An embodiment of a drug delivery device, indicated by reference number 11010, incorporating a 11600 temperature control system in accordance with the principles of the present disclosure is illustrated by Fig. 77. Although the 11600 temperature control system is described in conjunction with particular elements and features of the 11010 drug delivery device, the 11600 temperature control system can be implemented, where applicable, in any one of the disclosed drug delivery devices herein, including, but not limited to, any one of Drug Delivery Devices 10, 910, 2010, 6000, or 8000. Various elements of the device
169 Drug delivery 11010 are similar in structure and / or function to those previously described on the subject of drug delivery device 10. These items are assigned reference numbers similar to those previously provided with the addition of the two-digit suffix two " 11 ”, and, for brevity, are not described in detail below. For example, the drug delivery device 11010 includes a needle insertion mechanism 11200 that has at least some similarities in structure and / or function to the needle insertion mechanism 200 of the drug delivery device 10. It should be noted, however, that the 11600 temperature control system is not limited to being used in conjunction with elements of the drug delivery device 10, and can be implemented in any one of the drug delivery devices disclosed herein. , where appropriate.
Returning to Fig. 77, the drug delivery device 11600 may include a start button 11014, a drug container 11050, a drive mechanism 11100, a needle insertion mechanism 11200, a fluid path connector 11300 , a 11400 power and control system, and a 11600 temperature control system. Drug container 11050 may include a cylinder 11058 and a plunger seal 11060 movable through cylinder 11058 to discharge a drug from cylinder 11058, and a pierceable seal (not illustrated) to control access to an interior of cylinder 11058. The drive mechanism 11100 may include a drive housing 11130, a piston 11110 movable with respect to the drive housing 11130 and configured to impart movement to the piston seal 11060, and a piston thrust member 11106 disposed between the actuator 11130 and piston 11110. Fluid path connector 11300 can define a sterile fluid path between drug container 11050 and insertion mechanism 11200. The fluid path connector 11300 may include a connection hub 11310, a tubular conduit 11030 that provides fluid communication between connection hub 11310 and insertion mechanism 11200, and a drilling element (not shown) configured to drill The perforable seal to establish fluid communication between cylinder 11058 and tubular conduit 11030 during drug administration.
Tubular conduit 11030 may include a first flexible tube 11032, a second flexible tube 11034, and a rigid tube 11036 connected and providing fluid communication between the first and second flexible tubes 11032 and 11034. The first flexible tube 11032 can fluidly connect connection hub 11310 to a proximal end 11037 of rigid tube 11036, and the second flexible tube 11032 can fluidly connect needle insertion mechanism 11200 to a distal end 11038 of tube Rigid 11036. The first and second flexible tubes 11032 and 11034 can each be made of a material that is more flexible than the material used to construct the rigid tube 11036. In at least one embodiment, the first and
170 second flexible tubes 11032,11034 are made of a polymeric material, and the rigid tube 11036 is made of metal. As described below, the material used to construct the rigid tube 11036 can possess a relatively high thermal conductivity such that heat from a heating element can be transferred to a drug flowing through the rigid tube 11036 during administration.
An internal diameter of rigid tube 11036 may be less than an internal diameter of first flexible tube 11032 and / or second flexible tube 11034. Accordingly, rigid tube 11036 can serve as a flow restrictor that reduces and / or regulates the flow rate of the drug during administration. Rigid tube 11036 can be replaced by other rigid tubes that have different internal diameters depending on the target flow. Furthermore, the inclusion of a flow restrictor can provide expanded design space when coupled with other contributing elements such as a drive spring. In an alternative embodiment, the rigid tube 11036 may have an internal diameter that is equal to that of the first flexible tube 11032 and / or the second flexible tube 11034.
Still referring to Fig. 77, the temperature control system 11600 may include a heating element 11602, a first temperature sensor 11604, and a second temperature sensor 11606. In the illustrated embodiment, the heating element 11602 includes an electrically conductive coil that is wound around and contacts an exterior of rigid tube 10036. The heating element 11602 can be electrically connected to the power and control system 11400, so that the heating element 11602 is supplied with electricity from the power and control system 11400 in a controlled manner. The impedance of the material used to build the heating element 11602 can cause the heating element 11602 to convert at least some of the electricity supplied to heat. Due to the contact or close proximity of the heating element 11602 to the rigid tube 11036, the heat generated by the heating element 11602 can heat the rigid tube 11036, and due to the thermal conductivity of the rigid tube 11036, heating a drug flowing to through the rigid tube 11036.
The inclusion of heating element 11602 can eliminate the need for a pre-administration heating period in the event that drug delivery device 11010 has been removed from cold storage. Furthermore, heat transfer from heating element 11602 to the drug can be relatively efficient, because the volume of drug per unit length of rigid tube 11036 is relatively small. Thus, it may be possible to heat the drug to a target temperature without reducing the flow rate or increasing the length of the flow path. Therefore, it may be possible to heat the drug during administration without altering the duration of the
171 administration. In addition, heating element 11602 can be installed with little or no modification to a pre-existing fluid path connector, thus reducing manufacturing and / or design costs.
In some embodiments, the heating element 11602 can be dynamically controlled based on real-time drug temperature measurements to ensure that the drug is delivered to the patient at a desired temperature. As shown in Fig. 77, the first temperature sensor 11604 can be connected to the proximal end 11037 of the rigid tube 11036 so that the first temperature sensor 11604 can measure the temperature of the drug flowing in the rigid tube 11036. The second temperature sensor 11606 can be connected to the distal end 11038 of the rigid tube 11036 so that the second temperature sensor 11606 can measure the temperature of the drug leaving the rigid tube 11036. In some embodiments, the first and second temperature sensors 11604 and 11606 may not directly measure the temperature of the drug. Rather, the first and second temperature sensors 11604 and 11060 can measure the temperature of, respectively, the inlet and outlet portions of the rigid tube 11036 (or other portions of the drug delivery device proximate to the drug). These temperature measurements could be used to extrapolate the temperature of the drug based on the heat transfer characteristics of the material used to construct the rigid tube 11036 (or the other portions of the drug delivery device close to the drug).
The first and second temperature sensors 11604 and 11606 can output their temperature measurements to the 11400 power and control system, which can analyze temperature measurements to determine an amount of electricity to be supplied to heating element 11602 to achieve a target drug temperature. Additionally, the temperature measurements of the first and second temperature sensors 11604 and 11606 can be analyzed by the power and control system 11400 according to thermal dilution techniques in order to determine the flow rate of the drug. Furthermore, in an embodiment where the drug delivery device incorporates a motor controlled regulating mechanism to control the expansion of the piston thrust element (eg, similar to the 6000 or 8000 drug delivery device), the 11400 power and control system can control the motor based on the output of the first and second temperature sensors 11604 and 11606 to reduce the flow if the drug has not been sufficiently heated by the heating element 11602, so that the patient does not experience a painful injection due to cold temperatures. Furthermore, the input of the first and second temperature sensors 11604 and 11606 can be used to determine if the drug has been overheated by the heating element 11602 and is therefore no longer suitable for injection, in which case the drive mechanism 11100 can be
172 locked. Additional temperature sensors may be included to monitor the temperature of the drug in the container during, for example, storage to determine if the drug has been stored at an appropriate temperature. If not, the 11400 power and control system may lock the device and / or alert the patient that the drug is no longer viable.
The temperature monitoring system 11600 may further include temperature indicators (eg, lights, sounds, graphical displays, etc.) to inform the user of the drug temperature and / or whether the drug temperature is suitable for injection.
Although the embodiment of the tubular conduit illustrated in Fig. 77 incorporates two flexible tubes and a rigid tube connected therebetween, alternative embodiments may dispense with the rigid tube so that the tubular conduit is formed by a single unitary flexible tube. In such an embodiment, heating element 11602 can be wrapped around the single unitary flexible tube.
In an alternative embodiment, the power and control system 11400 can serve as a heating element 11602, or as a supplemental heating element. The 11400 power and control system may include a printed circuit and / or other electronics that heat up while performing its data processing functions. By positioning the printed circuit and / or other electronics immediately adjacent to tubular conduit 11030 (eg, immediately above tubular conduit 11030), the heat generated by the printed circuit and / or other electronics can be used to heat the drug as it flows through tubular conduit 11030. Therefore, in some embodiments, it may be desirable that the heat generated by the power and control system 11400 not be allowed to heat the drug. In such embodiments, the power and control system 11400 may include a heat sink that is remote from the drug container, the fluid path connector, and / or the insertion mechanism so that the heat sink can draw heat from the regions of the drug delivery device including the drug.
Although the heating element 11602 described above generates heat primarily through electrical resistance, other embodiments of the heating element can generate heat through other means, including, but not limited to, induction, the Peltier effect, and / or or a chemical reaction.
Furthermore, other embodiments of the temperature control system 11600 may include a refrigeration system (not shown) to reduce the temperature of the drug while it is disposed in container 11050 and / or flows through tubular conduit 11030. A Such cooling can employ a fan that captures cold air from outside the drug delivery device and / or blows hot air from inside the drug delivery device. Alternatively, or additionally, the cooling system
173 You can use the following to reduce the temperature of the drug: a thermoelectric cooling element that exploits the Peltiery effect / or a chemical reaction. XIII. Binding to the skin
The drug delivery devices of the present disclosure can be configured for temporary attachment to tissue of the patient's body (eg, the patient's skin) while the drug is administered. The drug delivery device can be attached to tissue of the patient's abdomen, thigh, arm, or some other portion of the patient's body. As described above, an adhesive patch (eg, adhesive patch 26) can be provided on or on a base of the housing to adhere the drug delivery device to the tissue of the patient's body. The adhesive surface of the adhesive patch may initially be covered by a non-adhesive patch liner (eg, non-adhesive patch liner 28), which is removed from the adhesive patch 26 prior to placing the drug delivery device in contact with the tissue from the patient's body.
Removing the adhesive from the tissue of the patient's body can cause discomfort to the patient, particularly if the adhesive interacts with a large surface area of the tissue of the patient's body. Therefore, to reduce the amount of body tissue in contact with the adhesive, only a limited portion of the base of the drug delivery device can be covered with the adhesive. Figs. 78A and 78B respectively illustrate adhesive patches 12000 and 12100 that reduce the amount of body tissue in contact with the adhesive, yet still provide adequate adhesion to secure the drug delivery device to the patient's body tissue during administration of drug. Adhesive patches 12000 and 12100 can each be applied to the base of any one of the drug delivery devices disclosed herein, including, but not limited to, any one of the drug delivery devices 10, 910 , 2010, 6000 or 8000.
Fig. 78A shows that adhesive patch 12000 includes an adhesive dot pattern 12002 with non-adhesive regions 12004 located in between. The illustrated pattern is symmetrical and includes equally spaced rows and columns of circular adhesive dots 12202. Alternative embodiments may have a non-symmetrical pattern and / or non-circular adhesive dots. Adhesive patch 12000 includes a base 12006 that has a first side (not shown) for attachment to the drug delivery device and a second opposite side 12006 that includes adhesive dot pattern 12002. In alternative embodiments, base 12006 can be omitted , and the adhesive dot pattern 12002 can be applied directly to an exterior surface of the drug delivery device.
In place of adhesive dots, adhesive patch 12100 shown in Fig. 78B
174 includes a plurality of adhesive strips 12102, with non-adhesive regions 12104 located therebetween. Adhesive strips 12102 are equally spaced and extend longitudinally through adhesive patch 12100. Alternate embodiments may have non-linear (eg, curved) adhesive strips and / or the adhesive strips may extend transversely through adhesive patch 12100. Adhesive patch 12100 includes a base 12106 that has a first side (not shown) for attachment to the drug delivery device and a second opposite side 12106 that includes adhesive strips 12102. In alternative embodiments, base 12106 may be omitted, and adhesive strip pattern 12102 can be applied directly to an exterior surface of the drug delivery device. A non-adhesive patch liner (eg, non-adhesive patch liner 28) can be used to cover the adhesive sides of each of the adhesive patches 12100 and 12200 before use.
Fig. 79 illustrates an embodiment of a non-adhesive patch liner, indicated by the reference number 12300, which includes stiffening elements 12310 to impart rigidity to the 12300 non-adhesive patch liner, in addition to an adhesive patch (eg, the adhesive patch 28,12100 or 12200) covered by 12300 non-adhesive patch coating. A body 12312 of the non-adhesive patch liner 12300 may be of the same length as the adhesive patch to prevent unintended adhesion prior to use of the drug delivery device. The stiffening elements 12310 can each be made of a more rigid material (eg, hardened metal or plastic) than the body 12312 of the non-adhesive patch liner 12300. Additionally, as shown in Fig. 79, each of the stiffening elements 12310 may have a tapered shape, with a width that narrows as the stiffening element 12310 approaches the outer peripheral edge of the body 12312. The stiffness imparted by the stiffening elements 12300 to the outer peripheral edge of the adhesive patch, which can extend beyond the outer edge of the body of the 12340 drug delivery device as shown in Fig. 79, makes the outer peripheral edge of the adhesive patch less likely to experience edge bending. Accordingly, stiffening elements 12310 can help the adhesive patch retain its flat shape so that the patient can press the adhesive patch directly against the tissue of the patient's body after removing the non-adhesive patch liner 12300.
Although the embodiment of the non-adhesive patch liner illustrated in Fig. 79 includes stiffening elements located at discrete points around the periphery of the non-adhesive patch liner, other embodiments of the non-adhesive patch liner may include a stiffening element which it continuously extends around the periphery of the non-adhesive patch liner. Fig. 80A illustrates an exploded view
175 computer the assembly of a 12400 non-adhesive patch liner, a 12500 adhesive patch, and a 12600 base of a drug delivery device. Adhesive patch 12500 may be similar to one of the adhesive patches disclosed herein, including, but not limited to, any one of adhesive patches 28, 12100, or 12200. Non-adhesive patch liner 12400 may include a core body portion 12402 and a ring-shaped stiffening portion 12404 positioned around the periphery of core body portion 12402 (as seen in the assembled view shown in FIG. 80B). The central body portion 12402 can cover a central portion of the adhesive patch 12500, leaving an outer peripheral edge of the adhesive patch 12500 exposed. The ring-shaped stiffening portion 12404 can be used to cover the exposed outer peripheral edge of adhesive patch 12500, thereby preventing it from bending at the edges. In some embodiments, the ring-shaped stiffening portion 12404 may cover and contact each of: an outer peripheral edge of the central body portion 12402, an outer peripheral edge of the adhesive patch 12500, and a base portion 12600 of the drug delivery device surrounding adhesive patch 12500. In such an embodiment, the underside of the ring-shaped stiffening portion 12404 may include an adhesive for adhering the ring-shaped stiffening portion 12404 directly to the base 12600 of the drug delivery device and the central body portion 12402. As such, removing the core body portion 12402 (eg, by pulling a tab extending from the core body 12402) can disengage the ring-shaped stiffening portion 12404 from the base 12600 of the drug delivery device, in addition to the adhesive patch 12500.
Although the stiffening elements described above can be joined or formed integrally with the non-adhesive patch liner, alternative embodiments of the stiffening elements can be joined or formed integrally with the adhesive patch. Fig. 81 Illustrates a 12710 drug delivery device (which may correspond to any one of the drug delivery devices disclosed herein, including, but not limited to, any one of the 10, 910 drug delivery devices. , 2010, 6000 or 8000) including a 12712 housing, a 12726 adhesive patch attached to the underside of the 12712 housing, and a 12728 non-adhesive patch liner movably attached to the underside of 12726 adhesive patch.
The adhesive patch 12726 may include a base 12730 and a plurality of stiffening elements 12732. The base 12730 may have a top surface 12734 rigidly attached to the bottom of the housing 12712 and a bottom surface (hidden in Fig. 81) covered with a leather adhesive. The 12730 base may have a larger footprint than the 12712 housing so that an external peripheral portion 12736 of the 12730 base forms a
176 skirt that extends beyond the outer edge of the 12712 housing.
Still referring to Fig. 81, stiffening elements 12732 may be formed in outer peripheral portion 12736 of base 12730. In the illustrated embodiment, stiffening elements 12732 and base 12730 are integrally formed such that elements stiffening 12732 and base 12730 form a single unitary structure made of a single material. Alternatively, stiffening members 12732 may be structures other than base 12730. As illustrated in Fig. 81, stiffening elements 12732 can be designed as a plurality of equally spaced ribs located at discrete locations around the periphery of base 12730. In addition, stiffening elements 12732 can protrude upward from the upper surface 12734 of the outer peripheral portion 12736 of the base 12730. However, the height of the stiffening elements 12732 can be such that the tops of the stiffening elements 12732 are located below the bottom surface of the casing 12712.
The reinforcing elements 12732 can transmit stiffness to the adhesive patch 12726 so that the adhesive patch 12726 can retain its generally flat shape. Accordingly, the periphery of adhesive patch 12726 is less likely to fold over or undergo curling when drug delivery device 12710 is being applied to the patient's skin or when non-adhesive coating 12728 is removed from the patch.
Referring to FIG. 82, in at least one embodiment, the non-adhesive coating 12728 of the patch may be comprised of the first spaced section 12740 and the second spaced section 12742 covering respective portions of the underside of the adhesive patch 12726. The first section 12740 may have a first tab 12744 protruding outward from one side of the adhesive patch 12726, and the second section 12742 may have a second tab 12746 protruding outward from an opposite side of the adhesive patch 12726. The first section 12740 and second section 12742 can be removed separately by pulling respectively first tab 12744 and second tab 12746, as described below with reference to FIGS. 83A-83C.
In at least one embodiment, the process of attaching the drug delivery device 12710 to the patient's skin 12750 may involve the following steps. Initially, the non-adhesive coating 12728 of the patch can be arranged against the patient's skin 12750. Thereafter, as the user or patient pushes down a first end 12752 of housing 12712 (opposite first tab 12744), first tab 12744 can be pulled outward to remove first section 12740 of non-adhesive liner 12728 from the adhesive patch patch 12726, as illustrated in FIG. 83A. Subsequently, while the user or patient pushes down a second end 12754 of the housing
177 12712 (opposite second leg 12746), second tab 12746 can be pulled out to remove second section 12742 of non-adhesive coating 12728 from adhesive patch patch 12726, as seen in FIG. 83B. This will result in the adhesive patch 12726 being flush with the patient's skin 12750, as shown in FIG. 83C.
In some embodiments, such as that illustrated in FIGS. 83A-83C, the first tab 12744 may be formed by a portion of the first section 12740 of the non-adhesive coating 12728 of the patch that folds back on itself. More specifically, the first section 12740 may have a first end 12760 in contact with the adhesive patch 12726 and a second end 12762 folded over the first end 12760 and configured to initially contact the patient's skin 12750. Second end 12762 may include first tab 12744. By pulling the first tab 12744 out, the first end 12760 of the first section 12740 can be unwound so that it detaches from the adhesive patch 12726. This configuration of the first section 12740 of the non-adhesive coating 12728 of the patch can facilitate removal of the first section 12740 of the adhesive patch 12726 even though the drug delivery device 12710 is pushed against the patient's skin 12750, as shown in FIG. 83A.
Similarly, the second tab 12746 may be formed by a portion of the second section 12742 of the non-adhesive coating 12728 of the patch that folds back on itself. More specifically, the second section 12742 may have a first end 12770 in contact with the adhesive patch 12726 and a second end 12772 folded over the first end 12770 and configured to initially contact the patient's skin 12750. The second end 12772 may include the second tab 12746. By pulling the second tab 12746 outward, the second end 12770 of the second section 12746 can be unwound so as to peel off the adhesive patch 12726. Like the first section 12740, this configuration of the second section 12742 of the non-adhesive coating 12728 of the patch may facilitate removal of the second section 12742 of the adhesive patch 12728 even though the drug delivery device 12710 is pushed against the skin 12750 of the patient, as shown in FIG. 83B.
Attachment of the drug delivery devices disclosed herein to the patient's body tissue is not limited to adhesive means. Instead of an adhesive patch, or as a complement to an adhesive patch, the drug delivery device may have a pneumatic system incorporated to temporarily fix the drug delivery device to the patient's body tissue. Such a pneumatic system may include at least one pressure communication channel or opening that extends through a base of the drug delivery device and distributes a negative fluid pressure through the base that draws body tissue against the base. . The realizations of said systems
178 Adhesives and / or tires for temporarily attaching a drug delivery device to body tissue are described in US Provisional Patent Application. No. 62 / 117,420 entitled DRUG DELIVERY DEVICE WITH VACUUM ASSISTED SECUREMENT AND / OR FEEDBACK, which is incorporated in its entirety by reference herein for all purposes. Any of the drug delivery devices disclosed herein, Including, but not limited to, any one of the drug delivery devices 10, 910, 2010, 6000, or 8000, may be configured to incorporate one or more of the Embodiments of the adhesive and / or pneumatic systems for temporarily affixing a drug delivery device to body tissue as described in US Provisional Patent Application. No. 62 / 117,420.
In still further embodiments, the drug delivery devices disclosed herein may be temporarily attached to a patient's soft body tissue by means of a mechanism (eg, a strap) that holds or tightens the drug delivery device. between the patient's soft body tissue and the bones or other more rigid anatomical structures behind the soft body tissue.
XIV. Connectivity aspects
The drug delivery devices of the present disclosure may be configured to include various data processing functionalities and / or operate within various data processing networks. In International Patent Application Publication No. WO / 2015/187793, International Patent Application Publication No. WO / 2015/187797, International Patent Application Publication No. WO / 2015/187799, the International Patent Application Publication No. WO / 2015/187802 and International Patent Application Publication No. WO / 2015/187805, each of which is incorporated herein by reference in its entirety to all effects, Embodiments of said functionalities and data processing networks related to drug delivery devices are disclosed. Any of the drug delivery devices disclosed herein, including, but not limited to, any of the drug delivery devices 10, 910, 2010, 6000, or 8000, can be configured to incorporate one or more of the functionalities of data processing and / or operating within one or more of the data processing networks disclosed in International Patent Application Publication No. WO / 2015/187793, International Patent Application Publication No. WO / 2015/187797, International Patent Application Publication No. WO / 2015/187799, International Patent Application Publication No. WO / 2015/187802, and International Patent Application Publication No. WO / 2015/187805.
The drug delivery devices disclosed in the present invention or the data processing systems in communication with the drug delivery devices
179 The drugs disclosed in the present invention can be configured to determine one or more states of the drug delivery device, the states of which can be determined by using one or more sensors in combination with one or more controllers. Sensors can rely on mechanical, electrical, or chemical detection mechanisms, and controllers can be mechanical, electrical, and / or electromechanical. By way of example and not by way of limitation, the states may refer to the operation of the drug delivery device and / or the condition of the drug delivery device. The drug delivery device or data processing system in communication with the drug delivery device can use status determination to control the operation of the drug delivery device and / or can communicate the status determination to other devices. such as third party servers that can further collect, process and / or broadcast the status determinations received from the drug delivery device. In at least one embodiment, the drug delivery device may communicate the status determination to one or more local computing devices, such as a mobile computing device (eg, smartphone, smart watch, tablet, laptop, etc.). .
In at least one embodiment, a drug delivery device in accordance with the present disclosure may communicate data related to the device or the patient to a supporting social network. For example, the drug delivery device may monitor a patient's use of the device with sensors or other means and link the patient to a support group that can encourage the patient to adhere to a treatment guideline (eg, a guideline therapy). In this way, the drug delivery device can take advantage of the capabilities of social media services (eg Facebook, Twltter, etc.) to identify a support group whose advice the patient is likely to follow, thus increasing the likelihood of that the patient complies with his treatment guidelines.
FIG. 84 illustrates an embodiment of a data processing network 13000 in communication with a drug delivery device 13100 corresponding to any one of the other drug delivery devices disclosed herein (including, but not limited to, any one of drug delivery devices 10, 910, 2010, 6000, or 8000). Drug delivery device 13100 is associated with a patient 13102 who can use drug delivery device 13100 to inject a drug as part of a treatment regimen. Drug delivery device 13100 can communicate with a server 13104 through one or more intermediate computing devices and / or one or more networks. In turn, server 13104 can communicate with drug delivery device 13100, patient 13102, and one or more computing devices (with associated parts) through one or more devices.
180 Intermediate computer scientists and / or one or more networks. As also illustrated in FIG. 84, server 13104 can communicate directly and / or wirelessly with portable drug delivery device 13100, using, for example, a 4G antenna.
Still referring to FIG. 84, the drug delivery device 13100 is illustrated in communication with a mobile computing device 13110 (eg, a smartphone) via a first communication link 13112 and with a computing device 13114 (eg, a personal computer or dedicated hub) via a second communication link 13116. Both links 13112 and 13116 can operate in accordance with a near field communication protocol, such as Bluetooth, for example. The mobile computing device 13110 can communicate with a cellular network 13118 through a communication link 13120, while the computing device 13114 can communicate with a wired network (eg local area network or wide area network) 13122 through of a communication link 13124. These networks 13118 and 122 can also communicate with server 13104.
Networks 13118 and 13122 can facilitate communication between server 13104 and one or more parties associated with patient 13102, such as their caregiver 13130, support staff 13132, and healthcare professional 13134, through their mobile computing devices. (for example, smart phones). Server 13104 may also be in communication with one or more computing devices (eg, servers) associated with one or more additional parts associated with patient 13102. For example, a server of the healthcare system 13140, a server, is illustrated. payment 13142, a pharmaceutical server 13144, a distribution server 13146 and a government agency server 13148 in communication with server 13104 through the 13122 network. It will also be recognized that networks 13118 and 13122 may be in communication with each other.
In at least one embodiment, the 13110 mobile computing device may include a processor (eg, microprocessor) and memory (eg, random access memory (RAM), nonvolatile memory such as a hard drive, flash memory , a removable memory, a non-removable memory, etc.) to store the computer-executable instructions to be executed by the processor. In some embodiments, the computer executable instructions may be included in a software application (eg, a mobile software application, also commonly called a mobile application) stored in the memory of the mobile computing device 13110. The software application may be installed on the mobile computing device 13110 as one or more download files, such as a download executable package installation file from a suitable application store via an Internet connection. Examples of package download files may include downloads through the ¡Tunes, Google store
181
Play Store, Windows Phone Store, downloading a package installation file from another computing device, etc. The software application may be developed for a mobile operating system such as Android ™ or iOS®, developed by Google and Apple, respectively. In some embodiments, the application may be started by a user by selecting an icon that appears on a home screen of a monitor (eg, a touch screen) of the 13110 mobile computing device. Various visualizations, including those with indications and / or informative instructions similar to those shown in the figures of International Patent Application Publication No. WO / 2015/187797, can be generated in the software application and displayed to a user and / or patient through the screen of the mobile computing device 13110.
XV. Energy management
As described above, the drug delivery devices of the present disclosure may incorporate a drive mechanism that includes one or more springs to provide energy intended to move a plunger seal to eject a drug from a container. The use of springs can offer simplicity and low cost benefits, but may have certain limitations.
There is a linear relationship between force and displacement in the spring actuators. To provide enough energy for drug release at the end of the plunger seal stroke, an excessive amount of energy can be introduced into the system when drug administration begins.
Furthermore, when higher viscosity drugs are administered through the drug delivery devices, the required spring forces can be increased. Springs with higher spring constants transmit more force to the drug product and container. Because the kinetic energy is proportional to the speed squared, even incremental increases in the spring constant can result in large changes in the net kinetic energy applied to the drug and the container.
This excessive energy may be felt by the patient as a slap or similar physical shock, as the spring-loaded piston impacts the plunger seal of the container that stores the drug. It is known that such mechanical shocks can also distract or disturb the users of the injectors and, therefore, can prevent a correct dosage of the dose. Thus, it is desirable to eliminate such disturbances.
Accordingly, there is a need for a drug delivery device with an energy management system that can maintain the expected spring force of the actuator mechanism while reducing the transmitted force and the resulting energy to the pharmaceutical product, thereby reducing the potential for damage. structural in the container or other components of the drug delivery device. Said supply device
182 The drug may potentially be more comfortable and safer to use, and applicable to a wider selection of drug.
The drug delivery devices of the present disclosure can be configured to include an energy management system that maintains the expected spring force load of the actuator mechanism while reducing the transmitted force and resulting energy to the drug product. In International Patent Application No. PCT / US15 / 29485 titled AUTOINJECTOR WITH SHOCK REDUCING ELEMENTS, and International Patent Application Publication No. WO / 2016/003813, International Patent Application Publication No. WO / 2015/187799, each of which is incorporated herein by reference in its entirety for all purposes, disclosures of such energy management systems. Any of the drug delivery devices disclosed herein, including, but not limited to, any one of the drug delivery devices 10, 910, 2010, 6000 or 8000, can be configured to incorporate one or more of the aspects, of the characteristics and / or functionalities of the energy management systems disclosed in International Patent Application No. PCT / US15 / 29485 and in International Patent Application Publication No. WO / 2015/187799.
FIG. 85A-85C, 86A-86C and 87A-87C illustrate, respectively, assemblies 14000a, 14000b, 14000c, each of which includes a 14050 drug container (which may, but is not limited to, any one of containers 50 , 618, 718, 818, 918, 1118 or 2050), a drive mechanism 14100 (which may correspond, but is not limited to, any one of drive mechanisms 100, 500, 1000 or 2100), a fluid path connector 14300 ( which may correspond, but without limitation, to any of the fluid path connectors 300, 622,722, 822, 922, or 2300) and a drive damping mechanism 14170a, 14170b, or 14170c that functions as an energy management system. Each of the assemblies 14000a, 14000b, and 14000c may be implemented in any one of the drug delivery devices disclosed herein, including, but not limited to, any one of the drug delivery devices 10, 910, 2010, 6000 or 8000.
Drug container 14050 may include a cylinder 14058 and a plunger seal 14060 movable through cylinder 14058 to discharge a drug 14038 from cylinder 14058 and a pierceable seal (not shown) that controls access to an interior of cylinder 14058. The actuator mechanism 14100 may include a drive housing 14130, a piston 14110 movable relative to drive housing 14130 and configured to transmit movement to piston seal 14060 and a piston thrust member 14106 disposed between drive housing 14130 and piston 14110. Piston 14110 may include a header 14148 disposed at its distal end.
183
The damper mechanism of the drive 14170 reduces the speed of the piston 14110 while retaining the intended force of the drive mechanism 14100, before the piston 14110 begins to move the piston seal 14060 distally through the cylinder 14058. By reducing the speed of the piston 14110, the damping mechanism 14170 essentially functions as a shock reducing element, as it reduces the kinetic energy applied to drug 14038 and drug container 14050. The damping mechanism 14170 can be adapted to reduce the speed of the piston 14110 in order to ensure that the pressure supplied to the system does not cause the syringe to break, that the pressure supplied to the system prevents a feeling of slapping or discomfort to the patient, and / or that the pressure delivered to drug 14038 prevents shear forces from damaging drug 14038.
In some embodiments, the drive damping mechanism can be adapted to reduce the piston speed by less than 1%. In other embodiments, the drive damping mechanism can be adapted to reduce the piston speed by approximately 1-5%. In additional embodiments, the drive damping mechanism can be adapted to reduce the piston speed by approximately 5-10%. In additional embodiments, the drive damping mechanism can be adapted to reduce the piston speed by approximately ΙΟΙ 5%. In additional embodiments, the drive damping mechanism can be adapted to reduce the piston speed by approximately 15-20%. In further embodiments, the drive damping mechanism can be adapted to reduce the piston speed by approximately 20-30%. In still other embodiments, the drive damping mechanism can be adapted to reduce the piston speed by approximately 30-50%. In still other embodiments, the drive damping mechanism can be adapted to reduce piston speed by approximately 51% -100%. The reduction in speed provided by the drive damping mechanism can be selected to avoid physical disturbance and / or patient discomfort by preventing the slap feeling and / or reducing breakage of the drug storage device, and / or reducing damage to the drug caused by shear loading, and / or allowing the injection device to be used to inject drugs with higher viscosities.
As shown in FIG. 85A-85C, the damper mechanism 14170 can be arranged in line between the gasket 14050 of the drug container plunger 14050 and the piston plunger head 14148 14110 to minimize the size of the assembly 14000a and more effectively damp the movement of the piston 14110 in the contact phase of the plunger head / plug. In other embodiments, as shown in FIGs. 86A-86C, the drive damping mechanism can be arranged in line between the end
184 proximal of the actuator mechanism piston 14110 and the main housing of the drug delivery device. In further embodiments, the drive damping mechanism may be integrated into the piston.
In accordance with various embodiments of assembly 14000a, damping mechanism 14170 may comprise a damper. The damper uses viscous friction to resist movement of piston 14110, thereby reducing the speed of piston 14110. FIGS. 85A-85C represent an illustrative embodiment of a linear damper 14172 that can be used in assembly 14000a. As shown, the linear damper 14172 includes a drive damper mechanism housing 14174, a working fluid 14178 contained within housing 14174, and a piston assembly 14176 movably disposed within housing 14174. Housing 14174 may comprise a 14174sw cylindrical side wall closed by each one of its first and second ends through a 14174ew terminal wall. In some embodiments, housing 14174 can be made of a rigid material, such as a plastic or metal. The working fluid 14178 contained within the housing 14174 may comprise, without limitation, oil (eg, mineral oil), silicone material, water, or air.
As shown in FIG. 85A-85C, the piston assembly 14176 may comprise a piston 14180 and a stem 14184 for pushing piston 14180 through housing 14174. In other embodiments, as shown in FIGS. 86A-86C, the piston rod can be configured and adapted to pull the piston through the damper housing 14174. As shown in FIG. 85A-85C, piston 14180 may comprise a single disk-shaped structure or element 14182 (piston disk element 14182) having front and rear surfaces 141821 and 14182t, respectively. The piston rod 14184 extends through an opening 14174a in one of the end walls 14174ew of the housing 14174, and may have one end attached to or unitary with the front surface 141821 or the rear surface 14182t of the piston disc element 14182, depending whether to push (see FIG. 85A-85C) or pull (FIG. 86A-86C) the piston disc member 14182 into the damping stroke. The free end of the piston rod 14184, which is normally disposed outside the housing 14174, can be attached to the piston head 14148, as shown in FIGS. 85A-85C. A seal, such as an O-ring (not visible), may be provided in or adjacent to opening 14174a to prevent working fluid 14178 from leaking out of housing 14174 between piston rod 14184 and opening 14174a in the end wall. 14174ew from housing 14174. In some embodiments, the piston assembly 14176 can be made of a rigid material, such as a plastic or metal. In other embodiments, the piston assembly 14176 can be made of an elastic material, such as a natural or synthetic polymer. In still further embodiments, the piston assembly 14176 may
185 be made of a rigid and porous material.
FIG. 85A-85C represent an illustrative mode of operation of damper 14172. As shown in FIG. 85A, upon actuation of the actuator mechanism, the power source (eg, piston thrust member 14106) of actuator mechanism 14100 advances piston 14110 toward piston seal 14060, disposed in cylinder 14058 of container 14050. drug. Once the linear damper 14172 contacts the piston seal 14060, as shown in FIG. 85B, the load from the piston thrust element 14106 begins to be transmitted to the linear damper 14172, thus causing the working fluid 178 in front of the damper piston disc element 14182 to be pushed or displaced through one or more constrictions to a location behind the piston disc element 14182, as the piston disc element 14182 moves from one end of housing 14174 to the other. The flow of working fluid 14178 through one or more constrictions generates viscous friction that resists movement of the piston disc member 14182, thereby damping movement of the plunger. In some embodiments where the piston disc element 14182 is made of a rigid material, the one or more constrictions may comprise a small gap (not shown) between the peripheral edge of the piston disc element 14182 and the side wall 174swdel damper housing 14174. In other embodiments, the one or more constrictions additionally or alternatively comprise one or more grooves 14186 provided at the peripheral edge of the piston disc element and / or one or more openings extending through the disc element 14182 of the piston through which the working fluid 178 flows as it travels from in front of the piston disk element 14182 to behind the piston disk element 14182. In other embodiments where the piston disc element 14182 is made of an elastic material, the peripheral edge of the piston disc element 14182 can be bent back enough to create a narrow gap or constriction between the peripheral edge of the piston element. Piston disc 14182 and side wall 174sw of damper housing 14174 (not shown) so that working fluid 178 can flow therethrough. In other embodiments where the piston disc element 14182 is made of a porous material, the working fluid 178 will flow through the pores (constrictions) of the piston disc element 14182. In each of these embodiments, one or more constrictions of the linear damper 14172 provide a velocity dependent resistance to the force of the power source 144 (eg, the piston thrust member 14106) acting on the piston 14110. This resistance, when coupled to the 14110 piston, reduces the speed of the 14110 piston while maintaining the strength of the power source 144 (for example, the piston thrust element 14106) before the 14110 piston begins to move the seal. Plunger 14060. The size, number and type of
186 Constraints, the type of working fluid 178 used in the linear damper 14172, the configuration of the housing 14174 and the piston assembly 14176, and any combination thereof, can be adjusted and / or selected to allow the damping characteristics of the Damping mechanism 14170 are tuned to adequately damp the shock characteristics of actuator mechanism 14100.
As shown in FIG. 85C, the piston disc element 14182 engages the front wall of the end walls of the damper housing 14174, and the force of the piston thrust element 14106 moves the piston seal 14060, the linear damper 14172 and the piston 14110 distally through cylinder 14058 of drug container 14050 at a reduced rate, to eject drug 14038 from cylinder 14058.
FIG. 86A-86C depict an illustrative mode of operation of a damper 14192 disposed in line between the proximal end 14146pe of the piston rod 14146 of the injection actuator mechanism and the main housing of the drug delivery device. In said embodiment, the damper housing 14194 can be retained in a tubular support element 14122 of the main housing by means of a retainer 14123 formed integrally with the tubular support element 14122. Said arrangement can be arranged on a cantilevered spring 14125 defined in the tubular support element 14122. The end of the piston rod 14204 disposed within the damper housing 14194 may be connected to the front surface 142021 of the piston disc member 14202, and the free end of the piston rod 14204 may be connected to the proximal end 14146pe of the piston rod 14146 piston, so that when the piston rod 14146 is actuated distally by the power source (for example, the piston thrust member 14106), The piston rod 14204 pulls the piston disc element 14202 through the damper housing 14194.
As shown in FIG. 86A-86C, upon actuation of the drive actuation mechanism, the energy source (eg, piston thrust member 14106) of the injection actuator mechanism begins to advance piston 14110 toward piston seal 14060, arranged in cylinder 14058 of drug container 14050. The load applied by the push member 14106 from the piston to the piston 14110 can be transmitted to the damper 14192. Working fluid 194 in front of piston disc element 14202 is pushed or displaced through one or more constrictions to a location behind piston disc element 14202 by pulling piston disc element 14202 from one end of the Damper housing 14194 to the other. The resistance generated by the working fluid 14198 flowing through one or more constrictions maintains the force of the piston thrust element 14106 while reducing the speed of the piston 14110 before the piston head element 14110 impacts with the piston seal 14060. The
187 Piston head element 14110 impacts piston seal 14060 at reduced speed, and the force of the power source (for example, piston thrust element 14106) begins to move piston seal 14060 and piston 14110 distally through cylinder 14058 of drug container 14050, to eject drug 14038 from cylinder 14058. At approximately the same time, the damper piston disc member 14202 14192 reaches the end of its stroke and engages the front end wall 194ew of the damper housing 14194. The energy source (eg, piston thrust member 14106) can be selected to apply enough energy to piston 14110 to overcome the holding and cantilever arrangement 123/125 so that shock absorber 14192 is released from the tubular support member 14122 to allow movement of piston 14110 when the power source (eg, piston thrust element 14106) drives piston 14110, seals piston 14060 and drug 14038 through cylinder 14058 of drug container 14050. Releasing shock absorber 14192 from tubular support member 14122 reduces the duration of the gear, allowing reduction of the overall length of the injection device.
FIG. 87A-87C represent an illustrative mode of operation of damper 14212 that is integrated into piston 14242. As shown in FIGS. 87A-87C, the integrated damper 14212 includes a housing 14214 formed by a tubular wall 14214t and a plunger head 14248, which closes the open distal end of the tubular wall 14214t. Damper 14212 further includes a piston formed by a distal end wall 14220 of hollow piston rod 14246, which is initially disposed at the proximal open end of tubular wall 14214t of damper housing 14214. The working fluid 14218 of the damper 14212 is initially provided in the damper housing 14214, in front of the distal end wall 14220 of the piston rod 14246. As shown in FIG. 87A, upon actuation of the actuator mechanism (not shown), the power source (eg, spring 14244s) of the injection actuator mechanism applies a force to piston rod 14246 and advances piston 14242 toward piston seal 14060 disposed in cylinder 14058 of drug container 14050. Once the plunger head 14248 contacts the plunger seal 14060, as shown in FIG. 87B, the spring load 14244s is transmitted to the damper 14212 integrally formed in the piston 14242. The working fluid 14218 located in front of the end wall 220 of the piston rod 14246 is pushed or displaced through one or more constrictions (as described above) arranged in the end wall 220 and in the space defined by the stem 14246. of the hollow piston, behind the end wall 220 as it moves distally to the damper housing 14214. The resistance or damping provided by damper 14212 reduces stem speed 14246
188 of the damper before the damper stem 14246 engages the damper head 14248 to move the piston seal 14060, and perform damping while maintaining spring force 14244s.
As shown in FIG. 87C, the end wall 220 of the piston rod 14246 engages the piston head 14248, which marks the end of the damper cushioning stroke. Spring 14244s then drives or forces piston rod 14246 and piston head 14248 as a single component (i.e., piston) against piston seal 14060 to drive piston seal 14060 distally through cylinder 14058 of the container. 14050 of drug, to eject drug 14038 from cylinder 14058.
FIG. 88 shows another illustrative embodiment of the damper. Shock 14270 is essentially similar to shock absorbers described above, except that the piston in piston assembly 14276 comprises two or more disc elements 14282 spaced from each other along piston rod 14284. The two or more piston disc elements 14282 and previously described constraints, which may be associated with each piston disc element 14282, provide a series of resistances to piston movement, each of which may be the same and / or different . The series resistance of the 14270 damper allows the piston speed to be reduced in stages or increments while maintaining the strength of the power source (eg, spring 14144s). In some embodiments, the multi-disc piston assembly 14276 can be made of a rigid material, such as a plastic or metal. In such embodiments, the one or more constraints, which control or define the resistance provided by each piston disc element 14282, may comprise a small gap (not shown) between the peripheral edge of one or more of the piston disc elements 14282 and the side wall 14274sw of the damper housing 14274. In other such embodiments, the one or more constrictions may comprise one or more grooves provided at the peripheral edge of one or more of the piston disc elements 14182, or one or more openings 14188 extending through the one or more piston disc elements 14182, one or more of the piston disc elements forming as porous discs, and any combination thereof. In other embodiments, the multi-disc piston assembly 14276 may be made of an elastic material, such as a natural or synthetic elastomer, so that the marginal peripheral edge of each disc element 14282 of the piston can bend back enough as to generate a small distance or constriction between the peripheral edge of the piston disc elements 14282 and the side wall 14274sw of the damper housing 14274, so that the working fluid can flow through it. If air is used as the working fluid, the elastic disc elements 282 of the piston of the piston assembly 276 can be used to create a squeezing film damping effect. Any of the
189 dampers described above with respect to FIGS. 85A-85C, 86A-86C and 87A-87C, may use the piston assembly 14276 of FIG. 88.
FIG. 89 shows an illustrative embodiment of the damper of the present disclosure. The damper 14370 comprises a housing 14374 and a piston assembly 14376 comprising a hollow piston rod 14384 and a piston configured as a bellows structure (bellows piston structure) attached to one end of the piston rod 14384 disposed within the housing 14374. Hollow piston rod 14384 may have an opening 14384a for the outlet of working fluid (not shown) flowing through hollow piston rod 14384 out of damper housing 14374. The bellows piston structure may comprise one or more collapsible lobes containing the working fluid, the fluid being capable of being air or any other suitable working fluid. An opening 14386 (constriction) may be provided in the portions of the lobe walls connecting each pair of adjacent lobes of the bellows piston structure to each other and to the hollow piston rod 14384. Openings 14386 allow the working fluid contained in the lobes to flow from one lobe to another, thereby functioning as constrictions. Damper 14370 provides cushioning when the bellows piston structure is pushed or pulled toward end wall 14374ew of damper housing 14374 and is contracted by the force acting on plunger 14142 supplied by the power source (e.g., spring 14144s) of the drive piston mechanism. The damping action is provided when the working fluid contained within the lobes flows through the openings 14386, the hollow piston rod 14384 and the opening 14384a of the piston as the lobes of the piston structure of bellows shrink. Any of the shock absorber embodiments described above with respect to FIGS. 85A-85C, 86A-86C and 87A-87C, may use the piston assembly 14376 of FIG. 89.
Turning to FIG. 90, actuator mechanism 100 and drug container 50 of FIG. 14A, equipped with an energy management system 15000. The energy management system 15000 includes a plurality of damping elements 15010a-e. The damping elements 15010a-e can be made of a shock absorbing material, such as rubber, plastic, or any other suitable material. The damping element 15010a is located on the contact surface between the piston extension 102 and the piston seal 60. The damping elements 15010b and 15010c are arranged on the outside of the cylinder neck 58. In an alternative embodiment, the damping elements 15010b and 15010c are replaced with a single ring-shaped damping element arranged approximately around the neck of the cylinder 58. The damping elements 15010d and 15010e are arranged on the surface of the distal end of the cap 52. In an alternative embodiment, the damping elements 15010d and 15010e are replaced with a
190 single ring-shaped damping element disposed on the surface of the distal end of the cap 52. In use, the damping elements l5010a-e can damp a shock wave created when the piston 110 impacts the piston seal 60, thereby reducing the likelihood of cylinder 58 breaking and / or causing the user to experience mechanical shock or a slap sensation.
Looking at FIG. 91A and 91B, actuator mechanism 2100, drug container 2150, and fluid path connector 2300 of FIG. 23A and 23B, equipped with a 16000 energy management system. The 16000 energy management system includes a plurality of damping elements 16010a-c. The damping elements 16010a-c can be made of a shock absorbing material, such as rubber, plastic, or any other suitable material. The damping element 16010a is placed on the contact surface between the piston 2110 and the piston seal 2060. The damping elements 16010b and 16010c are arranged on the surface of the distal end of the 23152 cap. In an alternative embodiment, the damping elements 16010b and 16010c are replaced with a single ring-shaped damping element arranged on the surface of the distal end of cap 2052. In use, the damping elements 16010a-c can dampen a shock wave created when the piston 2110 impacts the piston seal 2060, thus reducing the probability of cylinder 2058 rupturing and / or impacting the user mechanical or a slapping sensation.
XVI. Viscosity modeling
At least some embodiments described above or below may provide delivery devices capable of delivering a viscous liquid dosage form to a subject. At least some of these embodiments provide the subcutaneous injection of a large volume dose (eg, 2 ml to 2.5 ml or 2 ml to 3 ml) of a fairly viscous liquid with a tolerable level of pain to a subject. . Accordingly, at least some of the embodiments disclosed herein can administer the high volume viscous dosage form at such a rate that pain does not adversely affect adherence to the prescribed dosage regimen. Furthermore, at least some embodiments disclosed herein provide delivery devices capable of delivering a liquid dosage form (including a high volume dosage form) comprising an antibody, protein, peptide, or nucleic acid, for example.
At least one embodiment provides a delivery device comprising an insertion mechanism, a drive mechanism, and a sterile fluid pathway, wherein said device is configured to deliver a human patient from about 1.0 ml to about 2.5 ml, both inclusive, in a viscous pharmaceutical form at a speed
191 up to approximately 12 ml per minute. In certain embodiments, the delivery is subcutaneous injection. In at least one embodiment, the drug delivery device is a portable device. In particular embodiments, the device is pre-loaded with a dosage form. In some embodiments, the dosage form comprises a biological agent, such as an antibody, or antigen-binding portion thereof. In some embodiments, the dosage form comprises from about 50 mg to about 400 mg, inclusive, of a biological agent. In some aspects, the drug is administered at a fixed dose. In specific aspects, the drug is administered at a selected fixed dose of from about 50 mg to about 400 mg, inclusive; such as a fixed dose of about 50 mg, about 100 mg, about 150 mg, about 175 mg, about 200 mg, about 300 mg, or about 325 mg of drug / dose. In some aspects, the drug is administered in two or more doses. In other aspects, the drug is administered weekly, every two weeks, or monthly. In certain aspects, the drug is administered every two weeks. In some embodiments, the device is configured for the subcutaneous delivery of approximately 2 ml of a pharmaceutical form comprising approximately 300 mg of the drug. In some embodiments, the device is configured to deliver the dosage form once daily, twice weekly (biweekly), once weekly, biweekly (biweekly), once monthly, twice weekly month (biweekly), every two months (bi-monthly), or at a frequency determined by a health professional. In some embodiments, the delivery device is configured to deliver the dosage form at a preselected flow rate of the chosen flow rate from a range of about 0.167 ml per minute to about 12 ml per minute, inclusive. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 12 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of about 2 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 0.167 ml per minute. In some embodiments, the device is disposable.
At least one embodiment provides a drug delivery device comprising means for delivering to a human subject a volume of from about 1 ml to about 2.5 ml, inclusive, in a viscous dosage form at a flow rate of up to approximately 12 ml per minute. In certain embodiments, the delivery is subcutaneous injection. In some embodiments, the dosage form comprises a biological agent. The biological agent can be an antibody. In some embodiments, the pharmaceutical form
192 it comprises from about 100 mg to about 400 mg, inclusive, of a biological agent. In particular embodiments, the device is preloaded with a dosage form comprising a biological agent, such as an antibody. In some embodiments, the device is configured for the subcutaneous delivery of approximately 2 ml of a drug. In some embodiments, the device is configured to deliver the dosage form once a day. In some embodiments, the delivery device is configured to deliver the dosage form at a rate ranging from about 0.167 ml per minute to approximately 12 ml per minute, inclusive. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 12 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of about 2 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 0.167 ml per minute.
At least one embodiment provides a method of administration, to a human subject in need, of a dosage form comprising a viscous dosage form, comprising contacting a human patient with a drug delivery device configured to deliver from about 1 0.0 ml to approximately 2.5 ml, inclusive, of a viscous pharmaceutical form at a flow rate of approximately 12 ml per minute, and actuating said device to supply said pharmaceutical form. In certain embodiments, the delivery is subcutaneous injection. In some embodiments, the slimy dosage form comprises a biological agent such as an antibody. In some embodiments, the device is configured for the subcutaneous delivery of approximately 2 ml of a pharmaceutical form. In some embodiments, the device is powered once a day. In some embodiments, the rate of delivery (administration) ranges from about 0.167 ml per minute to about 12 ml per minute, inclusive. In some embodiments, the delivery rate is approximately 12 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of about 2 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 0.167 ml per minute.
At least one embodiment provides a delivery device comprising an insertion mechanism, a drive mechanism, and a sterile fluid pathway, wherein said device is configured to deliver, to a human patient, approximately 2 ml of a pharmaceutical form comprising a drug at a flow rate of up to approximately 12 ml per minute. In certain embodiments, the delivery is subcutaneous injection. In
193 In particular embodiments, the device is pre-loaded with a dosage form comprising a drug. In some embodiments, the dosage form comprises approximately 300 mg of a drug. In some embodiments, the device is configured to deliver the dosage form comprising a drug once a day. In some embodiments, the delivery device is configured to deliver the dosage form at a rate ranging from about 0.167 ml per minute to approximately 12 ml per minute, inclusive. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 12 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of about 2 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 0.167 ml per minute.
At least one embodiment provides a drug delivery device comprising a means for delivering a dosage form, to a human patient, of about 2 ml, comprising a drug, at a flow rate of up to about 12 ml per minute. In certain embodiments, the delivery is subcutaneous injection. In some embodiments, the dosage form comprises approximately 300 mg of a drug. In particular embodiments, the device is pre-loaded with a dosage form comprising a drug. In some embodiments, the device is configured to deliver the dosage form comprising a drug once a day. In some embodiments, the delivery device is configured to deliver the dosage form at a rate ranging from about 0.167 ml per minute to approximately 12 ml per minute, inclusive. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 12 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of about 2 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 0.167 ml per minute.
At least one embodiment provides a method of administration, to a human patient in need, in a pharmaceutical form comprising a drug comprising contacting a human patient with a drug delivery device configured to deliver approximately 2 ml of one form. pharmaceutical comprising a drug at a flow rate of up to about 12 ml per minute, and actuating said device to deliver said pharmaceutical form. In certain embodiments, the delivery is subcutaneous injection. In some embodiments, the device is powered once a day. In some embodiments, the dosage form comprises approximately 300 mg of a drug. In
194 In some embodiments, the device is configured to deliver the dosage form comprising a drug once a day. In some embodiments, delivery (administration) rates vary from about 0.167 ml per minute to about 12 ml per minute, inclusive. In some embodiments, the delivery rate is approximately 12 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of about 2 ml per minute. In some embodiments, the delivery device is configured to deliver the dosage form at a rate of approximately 0.167 ml per minute.
As used herein, viscosity generally refers to the state of having a thick, sticky, and semi-fluid consistency, corresponding to the informal concept of thick character. In particular, however, a fluid's viscosity is a measure of its resistance to gradual deformation by shear stress or tensile stress. Viscosity can be expressed as the amount of force required to overcome internal friction, for example, measured by force per unit surface that resists flow, where parallel layers separated by unit distance have a unit velocity relative to each other. The viscosity of a Newtonian fluid depends only on temperature, not on shear rate or time. The viscosity of non-Newtonian fluids, dependent on time, depends on temperature, shear rate and time; Depending on how the viscosity changes over time, the behavior of the fluids can be characterized as thixotropic (fluidization with time, that is, the viscosity decreases with time), rheopic (thickening with time, that is, the viscosity increases with time) or reotaxis (fluidization with time is correlated with the decomposition of the structure). The viscosity of non-Newtonian fluids, independent of time, depends not only on temperature, but also on shear rate. Viscosity can be measured in micropascals per second (mPa.s) (centipoise (cps)), where water is the standard at 1 mPa.s (1 cps). The blood has a viscosity of approximately 10 mPa.s (10 cps); maple syrup, from 150 mPa.s to 200 mPa.s (from 150 cps to 200 cps); SAE60 motor oil, from 1,000 mPa.s to 2,000 mPa.s (from 1,000 cps to 2,000 cps); ketchup, from 50,000 mPa.s to 70,000 mPa.s (from 50,000 cps to 70,000 cps); peanut butter, from 150,000 mPa.s to 250,000 mPa.s (from 150,000 cps to 250,000 cps); putty, from 5,000,000 mPa.s to 10,000,000 mPa.s (from 5,000,000 cps to 10,000,000 cps).
As noted above, temperature may be a factor in fluid mechanics of viscosity, but for the purposes of the analytical modeling described herein, temperature is assumed to be ambient and to remain essentially unchanged in the course of drug delivery. Experts in the field, provided with the
195 In this specification, they can adjust the settings of a drug delivery device to control, manage, or use changes in viscosity attributed to temperature. The viscous liquid as envisioned herein may be in a liquid form or reconstituted from a lyophilized form. Non-limiting examples of viscous fluids include those with at least about 10 mPa.s (10 cps) or about 100 mPa.s (100 cps) at a shear rate of 0.1 / second. An Illustrative viscosity may range from about 80,000 mPa.s (80,000 cps) to about 300,000 mPa.s (300,000 cps), inclusive, or the viscosity will be in the range of about 140,000 mPa.s (140,000 cps) to approximately 280,000 mPa.s (280,000 cps), inclusive, at a shear rate of 0.1 / second at 25 ° C or a viscosity range of approximately 100 mPa.s (100 cps) at approximately 1,000 mPa.s ( 1,000 cps), both inclusive, at a shear rate of 0.1 / second at 25 ° C. Viscosity can be measured with a rheometer.
The embodiments described herein provide a drug delivery device capable of subcutaneously delivering a 2 ml dosage form comprising 300 mg of a drug with acceptable pharmacokinetics and tolerability. In some embodiments, the pharmacokinetics and tolerability of the 2 ml injection are comparable to two subcutaneous injections of 150 mg drug / ml. Tolerability factors include local pain at the injection site and itching after injection at the injection site; local reactions at the injection site (eg, erythema, bleeding, rash, etc.) after injection; the presence of fluid leaks immediately after injection; and the incidence of adverse events emerging from treatment, including clinically significant changes in vital signs, physical examinations and laboratory parameters. Furthermore, the biomarkers relevant to the mechanism of action of a drug and the presence of antibodies against the drugs may be found acceptable in relation to the two-injection schedule. Therefore, the present embodiments provide drug delivery devices that allow a reduction in the number of injections by administering a larger dose volume of a rather viscous dosage form over longer injection time periods, while still meeting the requirements. pharmacokinetics, as well as pain tolerance by the patient.
Analytical models for delivery time (i.e., velocity), actuator system forces, and pressures in the main vessel may be useful in applying some of the embodiments described herein. For example, in fluid mechanics, the Reynolds number is a dimensionless quantity that is used to help predict similar flow patterns in different fluid flow situations. The
196 Reynolds number is defined as the ratio of driving forces (or inertial forces) to viscous forces, and quantifies the relative importance of these two types of forces for given flow conditions. Reynolds numbers are useful in performing the Fluid Dynamics Modeling Scale and, as such, can be used to determine the dynamic similarity between two different cases of fluid flow. This and other equations that relate to these analytical models include the following formulas:
Formula 1:
£ -4 1Π I where td is the supply time and R<sub>g</sub> is the geometric resistance of the fluid. TO<sub>pc </sub>is the surface of the primary container in m<sup>2</sup>; kds is the spring constant of the event in N / m; ZisubQ is the grouping term 1 subcutaneous delivery, in mm; Tf is the travel in the final position (end of the dose) in mm; T¡ is the path in the initial supply (after compression of the bubble) in mm.
Formula 2:
where ZisubQ is the grouping term 1 subcutaneous delivery, in mm; F<sub>or</sub> it is the force loaded in the housing in N; Ff<sub>g</sub> is the slip force in N; Ptb is the tissue back pressure in Pa (psi); Apc is the surface of the primary container in m<sup>2</sup>; and kds is the spring constant of the event in N / m.
Formula 3:
/1281^ 1231. 1231/. 1282 \
JL <sub>=</sub> I ----- 1 --- JL _--<sub>+</sub> ----- L | in which R<sub>g</sub> is the geometric resistance of the fluid; L<sub>n</sub> is the length of the needle in mm; Lt is the length of the tube; Lf<sub>r</sub> is the length of the flow limiter in mm; L<sub>c</sub> is the length of the cannula in mm; D<sub>n</sub> is the diameter of the needle in mm; Dt is the diameter of the tube in mm; Dfr is the diameter of the flow limiter in mm; and D<sub>c</sub> is the diameter of the cannula in mm.
Formula 4:
<img file="MX2018009826A_D0002.tif" />
where Re is the Reynolds number; Q is the flow in my per minute; p is the density of the fluid in kg / m<sup>3</sup>; μ is the dynamic viscosity in Pa «s (can also be calculated in cP, N» s / m<sup>2</sup> or kg / (m »s)); and D is the hydraulic diameter in mm (the wetted perimeter, total perimeter of all channels in contact with the flow [the diameter of the inner tube]). Can
197 it should be convenient to assume that the fluid has a density of 1.0 g / ml. The flow is laminar if the value is <2,300.
Tables and bar graphs representing variables, components, and delivery times for illustrative embodiments are shown in FIG. 92 to FIG. 99. For example, FIG. 98 shows the contribution to delivery time of groups of component parts which have been described in more detail above. Other data related to supply time, which are described in the tables above for four models (see Results: supply time, Case 1 to Case 4), appears as a bar graph in FIG. 92. The relationship between the force of the drive system and the travel distance of the supplied fluid is shown in FIG. 93. The four models were further analyzed for the contribution of the components to the delivery time in FIG. 94 (Case 1), FIG. 95 (Case 2), FIG. 96 (Case 3), FIG. 97 (Case 4) and FIG. 99 (Case 1). FIG. 94 and FIG. 99 allow comparison of the contribution of the components in the supply of fluids with different viscosities.
In one aspect of the present disclosure, a drug delivery device comprises an insertion mechanism, an actuator mechanism, a sterile fluid path, and a drug container comprising a dosage form comprising a drug, wherein said device is configured to Deliver 2 ml of the pharmaceutical form to a human patient at a flow rate of up to approximately 12 ml per minute. Furthermore, the drug delivery device may be configured for subcutaneous delivery. Furthermore, the drug delivery device can be configured to deliver approximately 300 mg of a drug. Furthermore, the drug delivery device may be configured to deliver the dosage form comprising a drug once a day. Furthermore, the drug delivery device may be configured to deliver the dosage form at a rate ranging from about 0.167 ml per minute to about 12 ml per minute, inclusive. Furthermore, the drug delivery device may be configured to deliver the dosage form at a rate of approximately 12 ml per minute. Furthermore, the drug delivery device may be configured to deliver the dosage form at a rate of about 2 ml per minute. Furthermore, the drug delivery device may be configured to deliver the dosage form at a rate of approximately 0.167 ml per minute. Furthermore, the drug delivery device may include a means for delivering a dosage form, to a human patient, of about 2 ml, comprising a drug, at a rate of up to about 12 ml per minute.
In another aspect of the present disclosure, one method includes administering, to a
198 human subject in need, in a pharmaceutical form comprising a drug comprising contacting a human patient with a drug delivery device configured to deliver approximately 2 ml of a pharmaceutical form comprising a drug at a flow rate of up to approximately 12 my per minute, and activate said device to supply said pharmaceutical form. Furthermore, the method may have delivery of a pharmaceutical form comprising approximately 300 mg of a drug. Furthermore, the method has the supply of a subcutaneous injection. Furthermore, the actuation step of the method can be carried out once a day. Furthermore, the delivery rate of the method can be from about 0.167 ml per minute to approximately 12 ml per minute, inclusive. In addition, the delivery rate of the method can be approximately 12 ml per minute, approximately 2 ml per minute, or approximately 0.167 ml per minute.
XVII. Additional Embodiment Mechanism Embodiments
At least some of the drug delivery devices described in the present application, including at least those described in connection with FIGS. 1-56, 74-91B, and 118-127D, may be configured to incorporate the embodiments of the insertion mechanism described below in relation to FIGS. 100A-117. The embodiments of the insertion mechanism described below in relation to FIGS. 100A-117 can be used to replace, in whole or in part, the insertion mechanism 200 previously described, the insertion mechanism 2000 or any other insertion mechanism described herein, when appropriate.
In one embodiment, insertion mechanism 17200 includes an insertion mechanism housing 17202, a housing cap 17203, a base 17252, and a sterile primer 17250, as shown in FIG. 100A. Base 17252 can be connected to mounting platform 1720 to integrate the insertion mechanism into drug delivery device 10 (as shown in FIG. 1A-1C). The connection of the base 17252 to the mounting platform 1720 may be, for example, such that the bottom of the base is allowed to pass through a hole in the mounting platform to allow direct contact of the base with the Diana. In such configurations, the bottom of the base 17252 may include a sealing membrane 17254 that, in at least one embodiment, can be removed prior to use of the drug delivery device 10. Alternatively, the sealing membrane 17254 may remain attached to the bottom of the base 17252 so that the hollow needle 17214 pierces the sealing membrane 17254 during operation of the drug delivery device 10. As shown in FIGS. 100A and 100B, the insertion mechanism 17200 may further include an insert deflection element 17210, a shaft 17212, a needle 17214, a retraction deflection element
199 17216, a clip 17218, a clip retention device 17219, a manifold guide 17220, septa 17230A and 17230B, and a collector body 17240. Collector 17240 may be connected to sterile fluid conduit 30 to allow flow to flow through the manifold 17240 into the hollow needle 17214 and into the target during drug delivery, as will be described in more detail herein.
FIG. 101-117 show the components of the insertion mechanism, according to at least a first embodiment, in greater detail. As shown in FIG. 101, the insert mechanism housing 17202 may be an essentially cylindrical component having an internal chamber within which the components of the insert mechanism are essentially housed. Housing 17202 further includes axial groove 17202B into which protrusion 17219H of clip retainer 17219 is slid during insertion, as will be described in greater detail below. Housing 17202 may further include circumferential groove 17202C that allows rotation of protuberance 17219H to allow retraction of needle 17214 by retraction deflection member 17216. Housing 17202 may further include axial slot 17202D into which sterile fluid conduit 30 can travel during needle insertion. Housing 17202 further includes one or more locking windows 17202A that are configured to engage locking pins 17208 in an initial, locked configuration. Lock pins 17208 can pass through windows 17202A into housing 17202 so that manifold guide ring 17220C rests on lock pins 17208 in an initial, locked configuration. Housing 17202 may further include limiting grooves 17202F and opening 17202E which are configured to accept and engage the travel limiter 17229. As an alternative, the 17219H boss can be replaced by a manual button or the like, or an automated or automatic mechanism responsive to a timer or other control system or method (not shown).
Housing cover 17203, shown in FIG. 102, contains guide protrusions 17204. Alternatively, guide protrusions 17204 may be a pre-formed appearance within housing 17202 of the insert mechanism. Guide protrusions 17204 are slidably engaged with clip retention device 17219 in steps 17219D and may be slidably engaged with manifold guide 17220 in steps 17220D on manifold guide ring 17220C. Insert deflection member 17210 is initially in an activated state between guide protrusions 17204 and the inner surface of insert mechanism housing 17202 and between the inner proximal end of insert mechanism housing cap 17203 and flange 17219E of the clip retention device 17219. Therefore, upon activation by the user, as described below, the deflection element of
200 Insert 17210 faces and exerts force on flange 17219E of clip retention device 17219 when insert deflection member 17210 is decompressed and / or deactivated, causing axial translation in the distal direction of clip retention device 17219, clip 17218, shaft 17212, retraction deviation element 17216, manifold guide 17220, and components retained within the lower chamber 17220E of the manifold guide. Prior to activation, insert deflection member 17210 is essentially maintained above closure windows 17202A in a compressed, activated state. Housing cap 17203 can be mounted to housing 17202 by any means known to a person skilled in the art such as threading, gluing, ultrasonic welding, snap fit, snap fit, etc.
FIG. 103 shows a clip 17218 according to an embodiment of the present disclosure. Clip 17218 includes opening 17218C through face 17218E through which needle 17214 can pass, and release surfaces 17218A and locking surfaces 17218B of arms 17218D. Clip 17218 also includes teeth 17218F. The cljp 17218 can be made of any number of elastic materials that are capable of flexing and essentially returning to their original shape. In an original form, clip 17218 can be flexed outward so that arms 17218D are not perpendicular to face 17218E. Clip 17218 is located within clip retention device 17219 such that clip 17218 is in fixed engagement with clip retention device 17219, but so that arms 17218D can flex within grooves 17219A. The teeth 17218F are configured to engage the grooves 17219F of the clip retainer 17219, thereby engaging the rotation of the clip 17218 and clip retainer 17219. In an initial locking stage, the retraction deflection element 17216 and shaft 17212 (with needle 17214 attached) are retained between release surfaces 17218A and face 17218E of clip 17218, and within inner chamber 17219B of the clip retention 17219. The needle can pass through opening 17218C of clip 17218, through opening 17219G of clip retention device 17219, and through manifold guide 17220 at septa 17230 and 17240. Septa 17230 is located within the manifold 17240, as shown in FIG. 106. The manifold 17240 further includes a manifold body 17240B having a manifold inlet 17240A into which the sterile fluid line 30 can be connected. This connection is such that sterility is maintained from the drug container 50 of the actuator mechanism 100, through the fluid path connection 300 and the sterile fluid line 30, in the sterile header 17242 of the collector manifold 17240 and sterile sleeve 17250 to maintain sterility of needle 17214 and fluid path to insertion into the target for drug delivery.
Clip retention device 17219, shown in FIG. 104. can include
201 a clip contact surface groove 17219A for the engageable retention of clip 17218, shown in FIG. 103. Flexible extensions 17219G may be configured to flex outwardly during installation of clip 17218 in slot 17219A of the clip contact surface and, after insertion of the clip, return to their natural positions. Therefore, clip 17218 is essentially maintained in an axial position with respect to clip retention device 17219. The clip retention device 17219 may have an inner chamber 17219B, within which retraction deflection member 17216, clip 17218, and shaft 17212 may encounter during an initial stage of operation lockout, and an outer upper chamber 17219C , which interfaces with insertion deflection element 17210. In at least one embodiment, insert deflection element 17210 and retraction deflection element 17216 are springs, preferably compression springs. Shaft 17212 may be engageably connected to a proximal end of needle 17214, such that axial displacement or translation of shaft 17212 causes movement relative to needle 17214.
The manifold guide 17220, shown in FIG. 105, may include a 17220A top boss and 17220B bottom chamber separated by a manifold guide ring 17220C. The upper boss 17220A is configured to engage the manifold 17240. The manifold guide ring 17220C is configured to be supported by locking pins 17208 in an initial, locking stage of operation.
As used herein, needle is intended to refer to a variety of needles including, but not limited to, conventional hollow needles, such as rigid hollow steel needles and solid core needles more commonly called trocars. Needle 17214 may include at least one side port 17214A for fluid admission into its hollow interior. Although only one such side port 17214A is illustrated, it will be appreciated that a plurality of side ports can be provided for fluid admission into the hollow interior of needle 17214. The needle can be any size needle suitable for the type of drug. and drug delivery (eg, subcutaneous, intramuscular, intradermal, etc.) desired.
After mounting, the proximal end of needle 17214 is maintained in fixed contact with shaft 17212; the proximal end of the needle can be capped (eg, a plastic cap, a bonding agent cap) or can be encapsulated within the 17212 shaft. By plugging the proximal end of the 17214 needle, it is prevented from Fluid exits the needle in this direction during drug delivery. The remainder of needle 17214 is allowed to pass through retraction deflection element 17216, opening 17218C of clip 17218, clip retaining device 17219, and manifold guide 17220. Needle 17214 may further pass through septa 17230, from manifold body 17240B through the header
202
17242 the collector, sterile sleeve 17250, and base 17252 through opening 17252A in the base. The septa 17230 and the collector body 17240B can be found within the lower chamber 17220B of the collector guide 17220 and within the sterile sleeve 17250 until the insertion mechanism operates. Similarly, the septum 17230A is essentially fixed and in sealing engagement within the upper part of the collector body 17240B, and the septum 17230B is essentially fixed and in sealing engagement within the lower part of the collector body 17240B to maintain sterility of the header 17242 of the collector. Upon insertion of needle 17214 into the target, port 17214A is located within manifold 17220 between the upper and lower septa. This allows fluid to pass into the needle to be delivered to the target.
The 17250 sterile sleeve is a collapsible or compressible sterile membrane that is fixedly meshed at a proximal end with the 17240 manifold and at a distal end with the 17252 base. In at least one embodiment, the 17250 sterile sleeve is held in a meshed fashion. Attaches to a distal end between base 17252 and insert mechanism housing 17202, as shown in FIGS. 108C, 109C and 110C. Base 17252 includes a base opening 17252A through which the needle can pass during operation of the insertion mechanism, as will be described later. The sterility of the needle is maintained by its initial positioning within the sterile parts of the insertion mechanism. Specifically, as described above, needle 17214 is maintained in the sterile environment of manifold header 17242 and sterile sleeve 17250. Opening 17252A in base 17252 can also be isolated from non-sterile environments, such as a 17254 sealing membrane.
FIG. 107 shows a travel limiter 17229, in accordance with at least one embodiment of the present disclosure. The 17229 travel limiter includes 17229A teeth and 17229C arms. Travel limiter 17229 is configured to mesh with housing 17202 such that arms 17229C are disposed, at least partially, within one or more lower circumferential grooves 17202F of housing 17202. Teeth 17229A are configured to mesh with opening 17202E of housing 17202. Teeth 17229A flex inward during insertion through opening 17202E due to interference with the walls of opening 17202E. Once the protuberances 17229D have completely passed through the opening 17202E, the teeth 17229A flex outward, essentially locking the travel limiter 17229 in place relative to the housing 17202. One or more are used proximal faces 17229B to restrict movement of the manifold guide 17220 and / or clip retention device 17219 as will be described in more detail below.
The operation of the insertion mechanism is described in this document
203 with reference to the above components, in view of FIG. 108-110. FIG. 108A shows an isometric view and FIG. 108B shows a cross-sectional view of the insertion mechanism, according to at least one embodiment of the present disclosure, in a locking and ready-to-use step. The locking pin / s 17208 is / are initially located within the locking windows 17202A of the housing 17202 of the insertion mechanism. In this initial position, the collector guide ring 17220C of the collector guide 17220, the clip retention device 17219, the clip 17218 and the shaft 17212 are kept above the closing windows 17202A and the / of the pins / is closure 17208. In this initial configuration, the insert deflection element 17210 and the retraction deflection element 17216 are each retained in their activated, compressed states. Protrusion 17219H is located within slot 17202B of housing 17202.
As shown in FIG. 1B, the locking pin (s) 17208 (not visible) can be moved directly by the user pressing the activation mechanism 14. As the user disconnects any safety mechanism, such as an optional sensor 24 ( shown in FIG. 1C), you can press the trigger mechanism 14 to start the drug pump. Pulsation of activation mechanism 14 can directly cause movement or displacement of control arm 40 and cause, directly or indirectly, displacement of locking pin / s 17208, from its initial position within closing windows. 17202A of the insert mechanism housing 17202. The displacement of the closing pin / s 17208 allows the insert deflection element 17210 to be decompressed and / or deactivated from its initial activated, compressed state.
As shown in FIG. 108B, the shaft protrusions 17212A maintain the retraction deflection element 17216 in a compressed state, activated between the shaft 17212 and the clip retention device 17219 17219 within chamber 17219B. Shaft 17212 is fixedly geared to the proximal end of needle 17214 at shaft inlet 17212B, placing shaft 17212 and needle 17214 in an initial position. Before operation, the sealing element 17254 can be removed from the bottom of the base 17252, and the base 17252 is contacted with the target injection site on the target. When the locking pin / s 17208 is / are displaced by the trigger mechanism, as described above, and the insert deflection member 17210 is allowed to expand axially in the distal direction (i.e. in the direction of the filled arrow of FIG. 108B), flange 17219E is forced by decompression and / or deactivation of insertion deflection member 17210 to translate axially in the distal direction to insert needle 17214 into the target. The axial translation of the clip retention device and the collector guide is directed and maintained in rotational alignment, through the interaction between the
204 Guide protrusions 17204 of the cover 17203 of the insertion mechanism housing and the corresponding steps 17219D and 17220D of the clip retention device 17219 and the manifold guide 17220. The release surfaces 17218A of clip 17218 engage shaft 17212 and retain retraction deflection member 17216 in a compressed, activated state, while manifold guide 17220 moves axially in the distal direction.
FIG. 109A shows an isometric view and FIG. 109B shows a cross-sectional view of an insertion mechanism in a delivery configuration, that is, with needle 17214 and shaft 17212 in a delivery position. In this position, the manifold guide 17220 is in contact with the proximal surfaces 17229B of the travel limiter 17229. As shown, sterile sheath 17250 is allowed to drop when insertion deflection member 17210 is expanded and needle 17214 is inserted into the target. At this stage, shown in FIG. 109, needle 17214 is inserted into the target for drug delivery. As the fluid path connection to the drug container is made and the actuator mechanism is activated, treatment with the drug fluid from the drug container is forced through the fluid path connection and the sterile fluid line to header 17242 of manifold and through needle 17214 for delivery to target. Accordingly, activation of the insertion mechanism inserts needle 17214 into a target or the target by placing the fluid path in communication with the target. As can be seen in FIG. 109B, arms 17218D flex inward due to contact with guide protrusions 17204. Therefore, release surfaces 17218A maintain contact with shaft 17212 and prevent retraction bypass element 17216 from being decompressed or deactivated. .
As shown in FIG. 110A-110B, needle 17214 retracts (ie, translates axially proximally) into housing 17202 of the insertion mechanism. FIG. 110A shows an isometric view of the insertion mechanism in this configuration, and Fig. 110B shows a cross sectional view. The cross sectional plane of FIG. 110B is not the same as that of FIG. 108B and FIG. 109B, but is rotated with respect to the cross section plane of those views. This retraction can be triggered by activation by the user, automatic retraction at the end of the dose delivery, failure or failure of the actuator, or upon activation of one or more sensors. Upon complete distal displacement of insert deflection member 17210, protrusion 17219H is essentially aligned with circumferential groove 17202C of housing 17202, and arms 17218D are constrained by guide protrusions 17204 as shown in FIGS. 11A-11B (position A). In this position, the clip retainer 17219 can rotate relative to housing 17202, housing cover 17203, and guide bosses 17204 to position B as shown in
205 FIG. 110A-B. Rotation of clip retainer 17219 is transmitted to clip 17218. In position B, arms 17218D of clip 17218 are no longer limited by guide protrusions 17204, therefore, arms 17218D flex radially outward ( that is, in the direction of the empty arrows shown in FIG. 109B) due to their outward branching. This causes release surfaces 17218A to disengage from shaft 17212. Upon disengaging the release surfaces 17218A from the shaft 17212, the retraction deflection member 17216 can expand axially in the proximal direction (ie, in the direction of the shaded arrow in FIG. 110B) from its activated state , compressed, initial. Retraction or axial translation of clip 17218 in the proximal direction is prevented by contact between locking surfaces 17218B and the distal ends of guide protuberances 17204, as shown in FIG. 110B. This locking also prevents axial movement in the proximal direction of the clip retention device 17219, the manifold guide 17220, and the elements of the insertion mechanism that are distal to (i.e., below) the 17220C guide ring. of the collector. In this configuration, needle 17214 is no longer exposed, thus making pump 10 safe to handle.
In a second embodiment, shown in FIG. 111, the insertion mechanism 172200 includes an insertion mechanism housing 172202, a base 172252 and a sterile cover 172250, as shown in FIG. 111Ay111B. Base 172252 may be connected to mounting platform 1720 to integrate the insertion mechanism into drug delivery device 10 (as shown in FIGS. 1A-1C). The connection of base 172252 to mounting platform 1720 can be, for example, such that the bottom of the base is allowed to pass through a hole in the mounting platform to allow direct contact of the base with the target. In such configurations, the bottom of base 172252 may include a sealing membrane 172254 that, in at least one embodiment, can be removed prior to use of drug pump 10. Alternatively, the sealing membrane 172254 may remain attached to the bottom of the base 172252 such that needle 172214 pierces the sealing membrane 172254 during operation of the drug pump 10. As shown in FIG. 111A and 111B, the insertion mechanism 172200 may further include an insertion deflection element 172210, a shaft 172212, a needle 172214, a retraction deviation element 172216, a clip 172218, a manifold guide 172220, a limiter 172229 of the traversal and a 172240 collector including a 172240B collector body, and septa 172230A and 172230B. Collector 172240 can be connected to sterile fluid conduit 30 to allow fluid flow through collector 172240, needle 172214 and into the target during drug delivery, as will be described in more detail herein.
206
As shown in FIG. 112, the insert mechanism housing 172202 may be an essentially cylindrical component having an internal chamber within which the components of the insert mechanism are essentially housed. Housing 172202 may further include axial slot 172202D into which sterile fluid passageway 30 can be translated during needle insertion, as will be described later. Housing 17202 further includes one or more locking windows 172202A that are configured to engage locking pins 17208 in an initial, locked configuration. Locking pins 17208 can pass through windows 172202A into housing 172202 so that manifold guide ring 172220C can rest on locking pins 17208 in a locked configuration, it begins. Housing 172202 may further include limiter slots 172202F which are configured to accept and engage the travel limiter 172229.
Housing 172202 may further include guide bosses 172204. Guide bosses 172204 may, alternatively, form part of a separate component located within housing 172202. Guide bosses 172204 are slidably engaged with manifold guide 172220 in steps 172220D. of the collector guide ring 172220C. Insert deflection element 172210 is initially in an activated state between guide protrusions 172204 and the inner surface of insert mechanism housing 172202 and between the proximal inner end of insert mechanism housing 172202 and manifold guide ring 172220C . Therefore, upon user activation, as further described below, the insert deflection element 172210 faces against and exerts force on the manifold guide ring 172220C as the insert deflection element 172210 decompresses. and / or deactivated, causing axial displacement of the collector guide 172220 and the components retained within the collector guide 172220. Prior to activation, insert deflection member 172210 is maintained essentially above closure windows 172202A in a compressed, activated state.
The manifold guide 172220, shown in FIG. 113 may include a clip retention device or part of a clip retention device 172219 and a lower chamber 172220B separated by a guide ring 172220C. The clip retention device or part of a clip retention device 172219 may include a clip contact surface slot 172219A for the engageable clip retention 172218. The flexible extensions 172219G may be configured to flex outward during the installation of the 172218 clip in the clip contact surface groove 172219A and, after insertion of the clip, return to their natural positions. Therefore, clip 172218 is essentially held axially with respect to manifold guide 172220. The clip retention device or
207 Part of a retention device 172219 may have an inner chamber 172219B, within which the retraction deflection element 172216, clip 172218, and shaft 172212 may encounter during an initial lockout stage of operation, and an outer upper chamber 172219C , which interfaces with insert deflection element 172210. In at least one embodiment, insert deflection element 172210 and retraction deflection element 172216 are springs, preferably compression springs. Shaft 172212 may be engageably connected to a proximal end of needle 172214 such that axial displacement or translation of shaft 172212 causes movement relative to needle 172214. The manifold guide ring 172220C is configured to support the locking pins 17208 in an initial, locking stage of operation.
Travel limiter 172229, shown in FIG. 114, may be configured to include a live hinge 172229D that allows the 172229C arms of the travel limiter 172229 to transform from a closed position, in which the proximal faces 172229B restrict the axial movement of the manifold guide 172220, in an open position , wherein the stroke limiter 172229 allows additional axial movement of the manifold guide 172220, thus allowing retraction of the needle. Travel limiter 172229 is configured to be, at least partially, inside housing 172202 in an initial, installed configuration. Upon transformation to its open position, travel limiter 172229 can be positioned essentially outside housing 172202 or may remain partially within housing 172202, but allows additional distal movement of manifold guide 172220. Alternatively, transformation from the closed position to the open position can be accomplished by moving the travel limiter 172229 in a direction perpendicular to axis A so that the proximal faces 172229B allow additional movement of the manifold guide 172220.
As used herein, needle is intended to refer to a variety of needles including, but not limited to, conventional hollow needles, such as rigid hollow steel needles and solid core needles more commonly called trocars. The needle may be any needle of adequate size for the type of drug and drug delivery (eg, subcutaneous, intramuscular, intradermal, etc.) desired. As with needle 17214 of the first embodiment, needle 172214 may include at least one side port 172214A for fluid admission into its hollow interior. Although only one such side port 172214A is illustrated, it will be appreciated that a plurality of side ports can be provided for fluid admission into the hollow interior of needle 172214. After mounting, the proximal end of needle 172214 is maintained in fixed contact with shaft 172212; the proximal end of the needle can be plugged with a plug (for example, a plastic plug, a binding agent plug), or it can be encapsulated within the 172212 shaft.
208 the proximal end of the needle 172214, fluid is prevented from leaving the needle in this direction during drug delivery. The remainder of the needle 172214 is allowed to pass through the retraction deflection element 172216, an opening 172218C of the clip 172218 and the guide 172220 of the manifold. Needle 172214 can further pass through septa 172230, from the collector body 172240B through the collector header 172242, through the sterile sleeve 172250 and through the base 172252 through the opening 172252A in the base. The septa 172230 and the collector body 172240B can be found within the lower chamber 172220B of the collector guide 172220 and within the sterile sleeve 172250 until the insertion mechanism operates. Similarly, the septum 172230A is essentially fixed and in sealing engagement within the upper part of the collector body 172240B, and the septum 172230B is essentially fixed and in sealing engagement within the lower part of the collector body 172240B to maintain sterility of the header 17242 of the collector. After insertion of needle 172214 into the target, port 172214A is located within manifold 172220 between the upper and lower septa. This allows fluid to pass into needle 172214 to be delivered to the target.
The 172250 sterile sleeve is a collapsible or compressible sterile membrane that is fixedly meshed at a proximal end with the 172240 manifold and at a distal end with the 172252 base. In at least one embodiment, the 172250 sterile sleeve is held in a meshed fashion. Attaches to a distal end between base 172252 and insert mechanism housing 172202, as shown in FIGS. 115A-C. Base 172252 includes a base opening 172252A through which the needle can pass during operation of the insertion mechanism, as will be described later. The sterility of the needle is maintained by its initial positioning within the sterile parts of the insertion mechanism. Specifically, as described above, needle 172214 is maintained in the sterile environment of manifold header 172242 and sterile sleeve 172250. The opening 172252A of the base 172252 can also be isolated from non-sterile environments such as a 172254 sealing membrane.
The operation of one embodiment of the insertion mechanism is described herein with reference to the above components, in view of FIG. 115AC. FIG. 115A shows a cross-sectional view of the insertion mechanism, according to at least one embodiment of the present disclosure, in a locking and ready-to-use step. The locking pin / s 172208 is / are initially located within the locking windows 172202A of the housing 172202 of the insertion mechanism. In this initial position, the collector guide ring 172220C of the collector guide 172220, the clip 172218 and the shaft 172212 are maintained above the closing windows 172202A and the closing pin (s) 172208. In this configuration initial, the deviation element of
209 Insert 172210 and Retraction Deflection Element 172216 are each retained in their activated, compressed states.
As shown in FIG. 1B, the locking pin (s) 172208 (not visible) can be moved directly by the user pressing the activation mechanism 14. As the user disconnects any safety mechanism, such as an optional sensor 24 ( shown in FIG. 1C), you can press the trigger mechanism 14 to start the drug pump. Pulsation of activation mechanism 14 can directly cause movement or displacement of control arm 40 and cause, directly or indirectly, displacement of locking pin / s 17208, from its initial position within closing windows. 172202A of the insert mechanism housing 172202. The displacement of the closing pin / s 17208 allows the insert deflection element 172210 to be decompressed and / or deactivated from its initial activated, compressed state.
As shown in FIG. 115B, the shaft protrusions 172212A maintain the retraction deflection element 172216 in a compressed state, activated between the shaft 172212 and the manifold guide 172220 within chamber 172219B. Shaft 172212 engages stationary to the proximal end of needle 172214 at shaft inlet 172212B. Before operation, sealing element 172254 can be removed from the bottom of base 172252, and base 172252 is contacted with the target injection site at the target. When the locking pin / s 172208 is / are displaced by the trigger mechanism, as described above, and the insert deflection member 172210 is allowed to expand axially in the distal direction (i.e. in the direction of the filled arrow of FIG. 115B), the guide ring 172220C is forced by decompression and / or deactivation of the insert deflection element 172210 to translate axially in the distal direction to insert the needle 172214 into the target. The axial translation of the collector guide is directed and maintained in rotational alignment, by the interaction between the guide protrusions 172204 of the insert mechanism housing 172202 and the corresponding steps 172220D of the collector guide 172220. Release surfaces 172218A of clip 172218 engage shaft 172212 and retain retraction deflection member 172216 in a compressed, activated state, while manifold guide 172220 moves axially in the distal direction. FIG. 115A shows a cross-sectional view of an insertion mechanism according to at least one embodiment in a delivery configuration, i.e. with needle 172214 and shaft 172212 in a delivery position. In this position, the manifold guide 172220 is in contact with the proximal surfaces 172229B of the travel limiter 172229. As shown, sterile sheath 172250 is allowed to drop when insertion diversion element 172210 is expanded and needle 172214 is inserted into
210 the Diana. At this stage, needle 172214 is inserted into the target for drug delivery. As the fluid path connection to the drug container is made and the actuator mechanism is activated, treatment with the drug fluid from the drug container is forced through the fluid path connection and the sterile fluid line to header 172242 of manifold and through needle 172214 for delivery to target. Accordingly, activation of the insertion mechanism inserts needle 172214 into a target, which may be, for example, a tissue, placing the fluid pathway in communication with the target. As can be seen in FIG. 115B, arms 172218D flex inward due to contact with guide protrusions 172204. Therefore, release surfaces 172218A maintain contact with shaft 172212 and prevent retraction bypass element 172216 from being unzipped or deactivated.
As shown in FIG. 115C, needle 172214 retracts (i.e., translates axially proximally) into housing 172202 of the insertion mechanism. This retraction can be triggered by activation by the user, automatic retraction at the end of the dose delivery, failure or failure of the actuator, or upon activation of one or more sensors. To effect retraction of needle 172214, the stroke limiter 172229 is displaced and / or transformed so that the guide ring 172220C on the manifold is no longer supported by proximal faces 172229B. Accordingly, further decompression or deactivation of the insert deflection member 172210 causes the manifold guide 172220 to move in the distal direction (the direction of the filled arrow of FIG. 115A). In this position, the arms 172218D of the clip 172218 are no longer limited by the guide protrusions 172204, therefore, the arms 172218D flex radially outward (ie, in the direction of the empty arrows shown in FIG. 115B). ) due to its derivation to the outside. This causes release surfaces 172218A to disengage from shaft 172212. Upon disengagement of the release surfaces 172218A from the shaft 172212, the retraction deflection member 172216 can expand axially in the proximal direction (ie, in the direction of the shaded arrow of FIG. 115C) from its activated state , compressed, initial. Retraction or axial translation of clip 172218 in the proximal direction is prevented by contact between locking surfaces 172218B and the distal ends of guide protrusions 172204, as shown in FIG. 115C. This blocking also prevents axial translation in the proximal direction of the manifold guide 172220 and the elements of the insertion mechanism that are distal to (i.e., below) the collector guide ring 172220C. In this configuration, needle 172214 is no longer exposed, thus making pump 10 safe to handle.
Activation of needle retraction can be accomplished through many
211 mechanisms. For example, a retraction activation mechanism such as a button can be provided on the outside of housing 12 that, when pressed by the user, activates retraction of the target needle. For example, in one embodiment, pulsation of the retraction trigger mechanism can cause clip retention device 17219 to rotate to position B, thereby allowing retraction deflection member 17216 to expand and retract needle 17214. In another embodiment, pulsation of the retraction trigger mechanism may cause displacement and / or transformation of the stroke limiter 172229 and allow the retraction deflection element 172216 to decompress and retract the needle. Actuation of the retraction activation mechanism can be spring assisted so as to reduce the travel and / or force required to press the retraction activation mechanism. Alternatively, or in addition, once the actuator mechanism 100 reaches the end of the dose of an electrical or mechanical actuator it may cause the retraction to activate. For example, at the end of the dose, an electrical connection can be made so that a current is applied to a nitinol component. After the current is applied, the temperature of the nitinol component rises. Due to the shape memory characteristics of nitinol, this component can be configured, after an increase in temperature, to transform from a first configuration to a second configuration. In this second configuration, the nitinol component may allow or cause actuation of the needle retraction, for example, by rotation of clip retainer 17219, or displacement or transformation of stroke limiter 172229.
Alternatively, or in addition, a sensor such as sensor 24 may, when drug pump 10 is withdrawn from the target, cause or allow activation of needle retraction. For example, when pump 10 is installed on the target, the position of sensor 24 can prevent retraction of the needle. Upon removal of the target, a change in the configuration of sensor 24 may allow retraction. In another embodiment, a light sensor can be placed in the drug pump 10, near opening 17252 in the base. When the drug pump 10 is in place on the target, the light would be essentially blocked preventing its entry into the sensor. By removing the drug pump 10 from the target, light can be detected by the light sensor, and the light sensor can cause an electromechanical actuator to allow or cause retraction activation. In other embodiments, a pin-type snap fit interconnect is used to initiate retraction of the needle. The pin can be deflected, at least partially, to protrude from housing 12 and be displaced upon placement of pump 10 on the target. When traveling, the pin can engage a female hole in a PCB that can be part of the Power and Control System 400. When removing pump 10 from the target, the offset pin disengages from the female PCB hole, making this
212 so that a signal triggers retraction of the needle.
Furthermore, the insertion mechanism may be configured such that the existence or detection of an unsafe condition, such as the displacement of the insertion mechanism with respect to housing 12 or platform 1720, causes actuation of retraction of the needle. For example, upon removal of the locking pins 17208 from the locking windows, the needle insertion mechanism may become free to float in a direction distal to housing 12 and / or platform 1720. A thrust element such that the needle insertion mechanism deviates to move in a distal direction with respect to housing 12 and / or platform 1720. However, when the pump 10 is placed on a target, movement is restricted by the target. Upon removal of the pump 10 from the target, the thrust element may be unzipped or deactivated and cause the needle insertion mechanism to move distally with respect to housing 12 and / or platform 1720. This distal displacement may cause or allow activation of retraction. Alternatively, or in addition, there may be an adhesive located on the distal face of the needle insertion mechanism that resists removal of the target and causes the needle insertion mechanism to move distally from housing 12 or platform 1720. Safety for the user can be improved through the use of one or more of these needle retraction mechanisms. For example, if drug pump 10 is inadvertently removed from the target after needle insertion, automatic retraction of the needle by one of the means described above reduces the risk of needle stick injury.
FIG. 116 shows an embodiment of a retraction trigger mechanism. The retraction activation deflection element 64 is connected at one end to the control arm 40 and, at the other end, to the connecting arm 78 of the pivot 70. The part 72 in contact with the target of the pivot 70 can extend to through the lower housing 12B and its movement can be restricted by contact with the target when the pump 10 is installed on the target. Pin 76 of pivot 70 is configured to mesh with housing 12 or another component of the pump, thereby allowing rotation of pivot 70 about pin 76. Extension 74 of pivot 70 is configured to contact protuberance 17219H during operation. Pulsation of activation mechanism 14 by the user causes displacement of slide 40, which activates the drug pump to insert the needle into the target by transforming closure pins 17208; pressing the trigger mechanism 14 can also activate the drug pump to perform additional actions. The displacement of the control arm 40 displaces the first end of the retraction activation deflection element 64, the displacement of the second end of the retraction activation deflection element is resisted by the
213 pivot 70 due to contact between the part 72 in contact with the target of the pivot 70 with the target. Upon removal of the drug pump 10 from the target, the pivot 70 can rotate and is rotated by the energy stored in the retraction activation deflection element 64. When pivot 70 rotates, extension 74 contacts protuberance 17219H and transfers rotation to clip retention device 17219, thereby causing or permitting retraction of the target needle.
Retraction of the needle may further be initiated after a failure and / or failure of the actuator mechanism 100. For example, the actuator mechanism may include a holding strap that serves to measure or control the rate of delivery of the contents of the container 50 of drug. The tension applied to, or maintained by, the tether strap can be controlled by one or more sensors. A reduction in tether strap tension may be an indication that the strap is not properly measuring or controlling the delivery of the medication. The sensor may be a mechanical component or link that is in contact with a part of the tether strap, at least partially controlling the contact position and / or configuration of the sensor. In response to a reduction in tension on the tether strap, the sensor transforms from a first position to a second position. This transformation can, directly or indirectly, cause retraction of the needle. Retraction can occur by a purely mechanical action or, alternatively, may involve an electrical signal received and / or generated by the power and control system 400.
In other embodiments, the sensor may be a strain gage, load cell, force sensor, or other sensor that is configured to measure and / or control the pressure, load, or tension present in the tether strap. In these embodiments, the sensor is at least partially attached to the tether strap and generates an electrical signal based on the tether strap tension. The electrical signal may vary in magnitude in proportion to the magnitude of the tension in the tether strap. Alternatively, the signal can be either interrupted or started when the tension in the tether strap falls below or exceeds a specified magnitude. The signal can be controlled by the power and control system which, based on the presence, absence or magnitude of the signal, can cause or allow retraction of the needle and / or cannula.
In still other embodiments, a mechanical failure of the tether strap can directly cause an electrical signal to start or stop. For example, the tether strap may be constructed, at least partially, of a conductive material. The tether strap may be in electrical communication with the power and control system. Mechanical failure of the tether strap can interrupt a current path through the tether strap and cause a change in current flow in one or more circuits. This change may initiate or allow retraction of the needle.
214
In addition, or alternatively, the position and / or speed of one or more features of the actuator system may be controlled by a sensor, such as: an optical sensor such as an encoder; a potentiometer; or a transducer. If the position and / or speed of the controlled feature exceeds or falls below a specified threshold, the power and control system may initiate and / or allow retraction of the needle.
A similar mechanism can be used to transform the travel limiter 172229 from a configuration where it restricts the axial movement of the manifold guide 172220 to a configuration where the collector guide 172220 is allowed to travel axially in the distal direction, allowing thus retracting the target needle. For example, the travel limiter 172229 can be flexed on the live hinge 172229D, causing the travel limiter 172229 to transform into its open position.
A method of operating an insertion mechanism in accordance with the present disclosure includes: removing the one or more locking pins from the corresponding one or more locking windows of an insertion mechanism housing, where the removal of said locking pins allows an insert deflection element to expand from its initially activated state; by actuating, by expanding the insertion deflection element, a clip retainer and a manifold guide axially in the distal direction to force a needle, at least partially, out of the insertion mechanism and toward a target; keeping the needle in a delivery position, as it would be when inserted into the target for fluid delivery; spin a clip retainer and a clip; allowing outward bending of a clip retained in a chamber of a clip retention device, wherein said clip initially retains a shaft and a retraction deflection member in an activated state and where the flex disengages one or more release surfaces of the clip from contact with a shaft, thereby allowing expansion of the retraction deflection member axially in the proximal direction; and retracting the needle after retraction of the shaft through a fixed connection between the needle and the shaft.
In another embodiment, a method of operating an insertion mechanism in accordance with the present disclosure includes: removing one or more locking pins from corresponding one or more locking windows of an insertion mechanism housing, where removal of said locking pins allow an insert deflection member to expand from its initially activated state; actuating, by expanding the insertion deflection member, a manifold guide axially in the distal direction to force a needle, at least partially, out of the insertion mechanism and toward the target; keeping the needle in an administration position for fluid delivery; transform or displace a travel limiter, allowing additional distal displacement of the collector guide; allowing outward bending of a clip held in a camera
215 of the collector guide, where said clip initially retains a shaft and a retraction deflection element in an activated state and where flexing disengages one or more clip release surfaces from contact with a shaft, thereby allowing expansion of the axially retracting deflection member in the proximal direction; and retracting the needle after retraction of the shaft through a fixed connection between the needle and the shaft.
Certain optional conventional components or variations of the drug insertion mechanism or pump 10 are contemplated always within the scope and scope of the present disclosure. For example, the upper or lower housings may optionally contain one or more transparent or translucent windows 18, as shown in FIGS. 1A-1C, to allow the user to view the operation of the drug pump 10 or verify that the drug dose has been completed. Furthermore, drug pump 10 may contain an adhesive patch 1726 and a patch liner 1728 on the underside of housing 12. Adhesive patch 1726 can be used to adhere drug pump 10 to the target for delivery of the dose. of drug. As one skilled in the art will readily understand, adhesive patch 1726 may have an adhesive surface for adhesion of the drug pump to the target. The adhesive surface of adhesive patch 1726 may initially be covered by a non-adhesive coating 1728 on the patch, which is removed from adhesive patch 1726 prior to placement of the drug pump 10 in contact with the target. Adhesive patch 1726 may optionally include a protective cover that prevents actuation of optional sensor 24 and covers the opening in the insert mechanism base. Removal of the liner 1728 from the patch can remove the protective cover or the protective cover can be removed separately. Removal of the coating 1728 from the patch can further remove the sealing membrane from the insertion mechanism, opening the insertion mechanism to the target for drug delivery.
Similarly, one or more of the components of the insertion mechanism and drug pump 10 can be modified while still being functionally within the scope and scope of the present disclosure. For example, as described above, although the drug pump housing 10 is shown as two separate components, the upper housing 12A and the lower housing 12B, these components may be a single, unified component. Similarly, although guide protrusions 172204 are shown as a unified preformed component of insert mechanism housing 172202, it may be a separate component fixedly attached to the interior surface of insert mechanism housing 17202. As described above, a glue, an adhesive, or other known materials or procedures can be used to secure one or more components of the insertion mechanism and / or the drug pump to each other. As an alternative, one or more components of the insertion mechanism and / or the
216 drug can be a unified component. For example, the upper housing and the lower housing may be separate components fixed together by an adhesive or adhesive ^ a fit & thread connection, an interference fit, a fusion joint, a weld, an ultrasonic weld, and the like; or the upper housing and the lower housing can be a single unified component. Such conventional components and functional variations would be appreciated by one of ordinary skill in the art and are therefore within the scope and scope of the present disclosure.
From the foregoing description, it will be appreciated that the insertion mechanisms and drug pumps disclosed herein provide an efficient and user-friendly system for automated drug delivery from a drug container. The novel embodiments described herein provide integrated security features; they allow direct activation by the user of the insertion mechanism; and are configured to maintain the sterility of the fluid path. As described above, built-in safety features include optional sensors, redundant locks, automatic needle insertion and retraction upon user activation, and numerous user interaction options, including visual interaction options and auditory. The new insertion mechanisms of the present disclosure can be activated directly by the user. For example, in at least one embodiment, the locking pin (s) that hold the insertion mechanism in its activated, locked state are moved directly from the corresponding locking windows of the insertion mechanism housing by pressing on the part of the activation mechanism user. As an alternative, one or more additional components may be included, such as a spring mechanism, which moves the locking pin (s) after direct movement of the activation mechanism by the user without intermediate steps.
In addition, the new configurations of the insertion mechanism and drug pumps of the present disclosure maintain sterility of the fluid path during storage, transport, and through operation of the device. Because the path the drug fluid takes within the device is fully maintained under sterile conditions, these components only need to be sterilized during the manufacturing process. Such components include the drug container of the actuator mechanism, the fluid path connection, the sterile fluid passage, and the insertion mechanism. In at least one embodiment of the present disclosure, it is not necessary to sterilize the power and control system, mounting platform, control arm, trigger mechanism, housing, or other components of the drug pump. This greatly improves the manufacturing capacity of the device and reduces mounting costs
217 associates. Accordingly, the devices of the present disclosure do not require terminal sterilization upon completion of assembly. An additional benefit of the present disclosure is that the components described herein are designed to be modular so that, for example, the housing and other components of the drug pump can be easily configured to accept and operate the insertion mechanism 17200, the insertion mechanism 172000, or a number of other variations of the insertion mechanism described herein.
The assembly and / or fabrication of the insertion mechanism, drug pump 10, or any of the individual components can utilize a number of materials and methodologies known in the art. For example, a number of known cleaning products, such as isopropyl alcohol, can be used to clean components and / or devices. Similarly, a number of known adhesives or glues can be used in the manufacturing process. Furthermore, known silicone fluids and processes can be employed during the manufacture of the novel components and devices. Furthermore, known sterilization processes can be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
The insertion mechanism can be mounted in a number of methodologies. In one method, a shaft is initially connected to a proximal end of a needle. The shaft and needle are inserted into an inner chamber of a clip retention device, where a retraction deviation element is maintained in an activated state between the clip retention device and the shaft. The shaft, needle, and retraction deflection element are held in this alignment by a clip, where the clip is fixedly and flexibly connected to the clip retention device at the clip contact surface. One or more septa are inserted into the collector to create a collector header. The collector and septum are inserted into a lower chamber of the collector guide, so that the needle pierces through the septum. A sterile sleeve is connected to the collector, where the needle is inside the sterile sleeve when the sterile sleeve is in an expanded configuration.
An insert spring is inserted into the insert mechanism housing between the housing and one or more guide protrusions which extend into the housing cover housing. The manifold guide and clip retention device, having the components attached thereto as described herein, are inserted into the insert mechanism housing so that the guide protrusions extend through the corresponding passages in one aspect of the clip retainer tab and manifold guide ring. When the clip retainer and the collector guide are translated in the proximal direction, the insert deflection member contacts the collector guide ring and is activated. When the transfer of the device
218 clip and collector guide retention and compression of the insert deflection element reach a point above one or more locking windows of the insert mechanism housing, one or more corresponding locking pins can be inserted to retain the collector guide in this position, and the insert deflection member in the compressed state activated. A travel limiter can also be inserted into the housing so that the teeth of the travel limiter mesh with the opening in the housing.
The distal end of the sterile sheath can be positioned and maintained in fixed engagement with the distal end of the insert mechanism housing by engaging the housing with a base. In this position, the sterile sheath is in an expanded configuration around the needle and creates an annular volume that can be sterile. A fluid line can be connected to the manifold at a manifold inlet so that the fluid path, when open, runs directly from the fluid line, through the manifold inlet, to the header of the manifold and through the needle. A fluid line connection can be connected to the opposite end of the fluid line. The fluid line connection, and specifically, a sterile fluid line connection sleeve, can be connected to a cap and pierceable seal of the drug container. The plunger seal and actuator mechanism can be connected to the drug container at an opposite end of the fluid path connection. A sealing membrane can be attached to the bottom of the base to isolate the insertion mechanism from the environment. The components that make up the path for fluid flow are already assembled. These components can be sterilized, by a number of known methods, and then either fixedly or removably mounted to a mounting platform or to the drug pump housing.
Manufacture of a drug pump includes the step of attaching the base of the insertion mechanism to a mounting platform or to the drug pump housing. In at least one embodiment, the joint is such that the base of the insertion mechanism can pass through the mounting platform and / or the housing to come into direct contact with the target. The manufacturing method further includes attaching the fluid path connection, drug container, and actuator mechanism to the mounting platform or housing. Additional components of the drug pump, as described above, including the power and control system, trigger mechanism, and control arm can be pre-attached, preformed, or mounted to the mounting platform or housing. An adhesive patch and the patch liner can be attached to the surface of the drug pump housing that contacts the target during device operation.
One method of operating the drug pump includes the steps of: activating,
219 by a user, the activation mechanism; move a control arm to operate an insertion mechanism; and actuating a power and control system to activate a drive control mechanism to drive the flow of drug fluid through the drug pump. The method may further include the step of: connecting an optional sensor before activating the trigger mechanism. Similarly, the method may include the step of: establishing a connection between a fluid path connection to a drug container. In addition, the method of operation may include moving a plunger seal into the drive control mechanism and the drug container to force the flow of drug fluid through the drug container from the fluid path connection. , a sterile fluid conduit and the insertion mechanism for delivery of the drug fluid to the target. The method of operation of the insertion mechanism and the drug pump can be better appreciated with reference to FIGS. 108-110 and FIG. 115, as described above.
In at least one embodiment, the present disclosure provides an insertion mechanism for a drug pump, said insertion mechanism including: an insertion mechanism housing having an internal chamber; a collector guide having an upper chamber and a lower chamber separated by a collector guide ring; one or more insertion deflection elements initially maintained in an activated state within the internal chamber of the insertion mechanism housing between the housing cover and the manifold guide ring; a flexible clip geared to the upper chamber of the manifold guide; a retraction deviation element and an axis connected to a proximal end of a needle, where the retraction deviation element is initially maintained in an activated state between the axis and the collector guide; and a collector having one or more septa, where the annular space between the septa defines a header of the collector.
In at least one embodiment, the insertion mechanism can include two or more insertion deflection elements. The manifold has a manifold inlet for connection to a fluid line. The insertion mechanism further includes a travel limiter, geared to the housing, at least a part of which is found within the internal chamber of the housing.
In another embodiment, the present disclosure provides an insertion mechanism for a drug pump, said insertion mechanism including: an insertion mechanism housing having an internal chamber; a housing cover meshed with the housing; a clip retention device including an internal camera and a tab; a collector guide having an internal chamber and a collector guide ring; one or more insertion deflection elements initially maintained in an activated state within the internal chamber of the insertion mechanism housing between the housing cover and the
220 clip retention device tab; a flexible clip meshed with the Internal chamber of the clip retention device; a retraction deviation element and an axis connected to a proximal end of a needle, where the retraction deviation element is initially maintained in an activated state between the axis and clip retaining device; and a collector having one or more septa, where the annular space between the septa defines a header of the collector. In an alternative embodiment, the insertion mechanism may include two or more insertion deflection elements. The manifold has a manifold inlet for connection to a fluid line. The insertion mechanism further includes a travel limiter, meshed with the housing, at least a part of which is found within the internal chamber of the housing.
The Insertion mechanism may further include a base connected to a distal end of the insertion mechanism housing. A sterile sheath can be fixedly connected between the collector and the base connected to a distal end of the insert mechanism housing. The term sterile sheath is used to describe a sheath within which certain internal components can be found, in one or more stages of operation, under sterile conditions. The cover does not have to be sterile throughout the entire operation of the mechanism or the pump and, in fact, may not initially be sterile until assembly and sterilization of certain components occurs. Furthermore, the term cover is not intended to mean any specific shape or configuration, but is used to describe a component that can provide an interior space within which other components can be found in one or more stages of operation.
One or more guide protrusions can extend from a proximal end of the insert mechanism housing or housing cover to the internal chamber. Alternatively, the one or more guide protrusions may be a separate component that is fixed to the insert mechanism housing. The collector guide ring and / or the clip retention device flange has one or more steps corresponding to the guide protrusions, where the collector guide and / or the clip retention device are slidably engaged with the housing by the interaction between the steps and the guide protrusions. The interaction between the steps and the guide protrusions can also work to maintain the rotational alignment of the manifold guide and / or to enhance the correct mounting of the components.
The clip may have one or more arms, each arm having a release surface and a locking surface. In an initial locked configuration, the release surfaces engage the shaft to keep the retraction deflection member in an activated state; and, in a retracted configuration, the release surfaces disengage from the shaft to enable deactivation of the retraction bypass element, thereby retracting
221 the shaft and the needle. The collector and the collector guide and clip retaining device are held in their end positions and their axial translation in the proximal direction is prevented by the interaction between the clip locking surfaces and the distal ends of the guide protrusions, blocking effectively additional movement of these components. In some embodiments, the clip is transformed or allowed to transform from the locked configuration to the retracted configuration by transforming the travel limiter from a first configuration to a second configuration. In the first configuration, the travel limiter restricts the distal movement of the collector guide and prevents the clip release surfaces from disengaging from the shaft. In the second configuration, the travel limiter allows some additional distal movement of the manifold guide allowing the clip release surfaces to disengage from the shaft. In other embodiments, the clip retention device is rotated from a first position to a second configuration; This rotation is transmitted to the clip. In the first configuration, the clip release surfaces are prevented from disengaging from the shaft. In the second configuration, the clip release surfaces are not prevented from disengaging from the shaft.
In another embodiment, the present disclosure provides a drug delivery pump with integrated safety features including a housing and mounting platform, on which an activation mechanism, an actuator mechanism, a fluid path connection can be mounted. , a power and control system, and an insertion mechanism for a drug pump, said insertion mechanism including: an insertion mechanism housing having an internal chamber; a collector guide having an upper chamber and a lower chamber separated by a collector guide ring; one or more insertion deflection elements initially maintained in an activated state within the internal chamber of the insertion mechanism housing between the housing cover and the manifold guide ring; a flexible clip geared to the upper chamber of the manifold guide; a retraction deviation element and an axis connected to a proximal end of a needle, where the retraction deviation element is initially maintained in an activated state between the axis and the collector guide; a collector having one or more septa, where the annular space between the septa defines a header of the collector; a travel limiter geared to the insertion mechanism housing and a base for connection of the insertion mechanism to the mounting platform.
In another embodiment, the present disclosure provides a drug delivery pump with integrated safety features including a housing and a mounting platform, on which an activation mechanism, an actuator mechanism, a fluid path connection can be mounted, a power and control system, and an insertion mechanism for a drug pump, including said delivery mechanism
222 insertion: an insertion mechanism housing having an internal chamber; a housing cover connected to the housing; a clip retention device having an internal chamber and a tab; a collector guide having an internal chamber and a collector guide ring; one or more insertion deflection elements initially maintained in an activated state within the internal chamber of the insertion mechanism housing between the housing cover and the manifold guide ring; a clip flexibly engaged with the internal chamber of the clip retention device; a retraction deviation element and an axis connected to a proximal end of a needle, where the retraction deviation element is initially maintained in an activated state between the axis and the clip retention device; a collector having one or more septa, where the annular space between the septa defines a header of the collector; a travel limiter geared to the insertion mechanism housing; and a base for connecting the insertion mechanism to the mounting platform.
The drug pump insertion mechanism may further include a base connected to a distal end of the insertion mechanism housing. The manifold can have a manifold inlet for connection to a fluid conduit, where the fluid conduit can be used for fluid transfer between the fluid path connection and the insertion mechanism. A sterile sheath can be fixedly connected between the collector and the base connected to a distal end of the insert mechanism housing. These components function to maintain the sterility of the fluid path and the needle, prior to insertion into the target.
In a further embodiment, the present disclosure provides a method of mounting the insertion mechanism that includes the steps of: connecting a shaft to a proximal end of a needle; inserting the shaft and needle into an inner upper chamber of a collector guide, where a retraction deviation element is maintained in an activated state between the collector guide and the axis, and is maintained in the activated state by a connected clip of fixed and flexible to the guide manifold on a contact surface of the clip. The method further includes: inserting one or more septa into the collector to create a collector header in between, and then inserting the collector and the septa into a lower chamber of the collector guide so that the needle pierces through of at least one septum and is initially, at least partially, within the header of the collector. In addition, the method includes: inserting an insert deflection member into an insert mechanism housing between the housing and one or more guide protrusions extending into the housing from a proximal end or from a housing cap; inserting the collector guide into the insert mechanism housing so that the guide protrusions extend through corresponding passages in one aspect of the guide guide collector guide ring
223 collector, where when the collector guide is translated in the proximal direction, the insert deflection element contacts the collector guide ring and is activated.
In an alternative embodiment, the present disclosure provides a method of mounting the insertion mechanism that includes the steps of: connecting a shaft to a proximal end of a needle; inserting the shaft and needle into an internal chamber of a clip retention device, where a retraction deviation element is maintained in an activated state between the clip retention device and the axis, and is maintained in an activated state by a clip fixedly and flexibly connected to the clip retention device on a clip contact surface. The method further includes: inserting one or more septa into the collector to create a collector header in between, and then inserting the collector and the septa into a lower chamber of the collector guide so that the needle pierces through of at least one septum and is initially, at least partially, within the header of the collector. In addition, the method includes: inserting an insert deflection member into an insert mechanism housing between the housing and one or more guide protrusions extending into the housing from a proximal end or from a housing cap; inserting the clip retainer and the collector guide into the insert mechanism housing so that the guide protrusions extend through corresponding passages in a flange aspect of the clip retainer and collector guide ring of the collector guide, where when the clip retainer and the collector guide are moved in the proximal direction, the insert deflection element contacts the tab of the clip retention device and is activated.
Upon transfer of the manifold guide and / or clip retaining device, and compression of the insert deflection member to a point above one or more closure windows of the insert mechanism housing, the method includes stage of: Place one or more corresponding closing pins in the closing windows and in removable gear with the collector guide to retain the collector guide in this position and the insert deflection element in the activated state. Finally, a base can be attached to the distal end of the insert mechanism housing to hold the components in place. The mounting method may further include the step of: engaging a sterile sleeve fixedly at an end proximal to the manifold and into a fixed gear at an end distal to the base. Similarly, the method may include: attaching a fluid line to the manifold at a manifold inlet. The mounting method may further include the step of: attaching a travel limiter to the housing, such that at least a portion of the travel limiter is inside the housing.
In yet another embodiment, the present disclosure provides a method of operating the drug delivery pump. The method of operation includes:
224 displacing an activation mechanism to disengage one or more locking pins from the corresponding closing windows of an insert mechanism housing, where said disengagement allows an insert deflection member to expand in a distal direction essentially along a longitudinal axis of the insertion mechanism from its initial activated state, where said expansion activates the insertion of a needle into the target; connecting a fluid path connection having a piercing element to a drug container having a pierceable seal; and activating a drive mechanism to force a fluid through the fluid path connection, the needle and into the target. The method also includes: disengaging one or more release surfaces of a clip from its engagement with a shaft retained within a manifold guide or clip retention device within the insert mechanism housing, where such disengagement allows the retraction deflection member to expand into one proximal direction essentially along a longitudinal axis of the insertion mechanism housing from its initial activated state, where said expansion activates the retraction of the needle. In a preferred embodiment, the method of operation may include: first moving one or more sensors to allow movement of the trigger mechanism. The method may include one or more additional steps to activate the needle retraction. These steps can be performed by the user, such as, for example, moving a second activation element, or they can be performed automatically by the drug pump once the dose delivery has been completed, when an insufficiency or failure occurs in the drive mechanism or upon removal of the drug pump from the target.
XVIII. Additional Embodiments of Fluid Path Connector
At least some of the drug delivery devices described in the present application, including at least those described in connection with Figures 1-47, 74, 75, and 77-117, can be configured to incorporate the connector embodiments of fluid pathways described below in relation to Figures 118-127D. The connected fluid path embodiments described below in relation to Figures 118-127D can be used to replace, in whole or in part, the fluid path connector 300 described above, the fluid path connector 622, the fluid path connector 722, the fluid path connector 922, the fluid path connector 1122, the fluid path connector 2300, or any other fluid path connector described herein, where appropriate.
As discussed above, in the process of filling drug containers and other drug delivery devices, it is sometimes necessary to connect two or more sterile components or subassemblies. For example, wearable drug injectors or pumps may include a drug container that can be filled with a
225 Fluid drug using conventional aseptic pharmaceutical filling completion processes. After filling the drug container, it may be necessary to connect the drug container to one or more additional components or subassemblies such that fluid communication can be established between the drug container and these components. Maintaining the fluid path under aseptic conditions is critical, avoiding the introduction of harmful microbes into the drug and / or the fluid path. The connection of two or more aseptic components or subassemblies is generally carried out in an aseptic environment, thereby ensuring that no harmful foreign matter is introduced into the assembly. This, however, was to lead to an increase in the manufacturing cost of the drug delivery devices. The fluid path fittings of the present disclosure can be mounted to the drug container in a non-aseptic environment while maintaining aseptic conditions of the fluid path and drug fluid.
As shown in the embodiment of Figures 118-120, the drug container 1850 may consist of an 1858 barrel, an 1852 stopper, and an 1856 pierceable seal. The 1856A base of the 1856 pierceable seal may be in sealed engagement with the interior. of the 1858 barrel. The 1852 stopper can be fixedly attached to the outside of the 1858 barrel and can retain the 1856 pierceable seal in position and restrict movement of the 1856 pierceable seal relative to the 1858 barrel. Plug 1852 may include one or more closure arms 1852A extending from ring 1852B of plug 1852 substantially parallel to axis AA and in a distal direction. The closing arms 1852A may include a protrusion 1852C that extends radially to or near its distal ends. The drug container may further include an 1857 toroidal seal. In an initial configuration, shown in Figure 118, the toroidal seal is retained between protrusions 1852B and proximal circumferential rib 1856B of pierceable seal 1856. Pierceable seal 1856 may further include a distal circumferential rib 1856C that further retains the toroidal seal 1857. By placing the toroidal seal in position when the drug container is in an aseptic environment the portion of pierceable seal 1856 contacts the inner face of toroidal seal 1857 (i.e., the area between the proximal circumferential rib and the distal circumferential rib ) is maintained in aseptic conditions even if the drug container is moved to a septic environment.
Fluid path connection 18300 includes connecting shaft 18310, retainer 18320, piercing member 18330, and plug seal 18330. As shown in Figure 120A, plug seal 18330 is initially disposed within bore 18310A of connecting shaft 18310. When the fluid path connection is mounted, the plug seal maintains the aseptic condition of at least a portion of the fluid path connection by maintaining a sealed coupling with the 18310A drill. The retainer is arranged for sliding translation with respect to the connecting axis 18310 in a direction parallel to the axis BB (shown in
226 Figure 120D). Initially, the movement of the 18320 retainer can be restricted. The restriction may be due to the coupling of the flexing arms 18320B with grooves in the connecting shaft 18310. Piercing member 18330 can be fixedly coupled to retainer 18320 such that translation of retainer 18320 is transferred to the piercing member. The piercing member may be attached, snap-fit, or attached to the retainer using appropriate means. The piercing member may initially be disposed at least partially within a cavity 18310D and / or an opening 18310C of the connecting shaft 18310. Both cavities 18310D and 18310C are maintained in aseptic condition by seal 18340 on the plug. Retainer 18320 may further include a conduit connection 18320A to which sterile fluid conduit 30 can be attached (see Figure 1B). This provides a sterile fluid path from the sterile fluid path connection to the insertion mechanism. Piercing member 18330 may be a hollow needle such that fluids can pass through the interior of the piercing member gap and into the sterile fluid passage.
Figures 120A-D shows the steps of connecting the fluid path connection to the drug container. This connection can be carried out in a non-aseptic environment. In Figure 120A, the fluid path connection plug seal is basically aligned with the AA axis (ie, plug seal 18340 is aligned with the distal end of pierceable seal 56). FIG. 120B shows a cross sectional view of the fluid path connection 18300 in contact with the drug container. The slots 18310B of the connecting shaft 18310 are aligned with the closing arms 1852A, this alignment guides the installation of the fluid path connection and prevents rotation of the fluid path connection with respect to the drug container. As shown in Figure 120C, as the connection shaft is moved in the proximal direction along the AA axis, stopper seal 18340 is prevented from moving with the connection shaft due to contact with the pierceable seal 1856. This causes the plug seal to shift out of position within drill 18310A. In addition, the shoulder 18310E contact of the connecting shaft 18310 with the 1857 toroidal seal causes the toroidal seal to translate in the proximal direction along the AA axis. As the connecting shaft travels along the AA axis only drill 18310A comes into contact with the part of the pierceable seal that was previously covered with the 1857 toroidal seal. Furthermore, as the connection shaft comes into contact with the toroidal seal these components are coupled in a sealed manner such that microbes and other foreign substances cannot come into contact with the sterile parts of the pierceable seal and the connection of fluid path. Thus, the aseptic conditions of the 1856 pierceable seal, opening 18310C, cavity 18310D, and piercing member 18330 are maintained during the installation of the fluid path connection.
227
As seen in Figure 120D, proximal translation of the connection axis brings the connection axis into contact with a portion of drug container 1850, thereby preventing further distal translation of the connection axis. In the shown embodiment, the connecting shaft contacts a portion of the plug 1852. When the connecting shaft reaches this position, the plug seal can be removed from the assembly and discarded. Quick release arms 1852A can engage one or more aspects of the connecting shaft and thereby prevent the connecting shaft from being removed from the drug container.
After installation, the piercing member aligns with the sterile portion of the pierceable seal that had originally mated with the toroidal seal. The components can be mounted on the drug delivery device 10 (see Figures 1A-1C) and remain in this configuration until activation of the drug pump by the user. After activation, the retainer 18320 translates in a direction parallel to the BB axis with respect to the connecting axis, causing the piercing member 18330 to translate. Due to this translation, the piercing member contacts and subsequently pierces the 1856 pierceable seal. This opens a fluid path from the drug container and through the piercing member. The fluid path may further include the sterile fluid conduit 30 (see Figure 1B) which mates with the 18320A retainer conduit connection 18320. This provides a sterile fluid path from the drug container to the delivery mechanism. insert for supply to the patient.
Figures 121A-121B show another embodiment of the present disclosure in which the connecting shaft 181310 includes quick-closing arms 181310F that can engage the cap 181052 of the drug container 181050. Toroidal seal 181057 is initially retained between proximal circumferential rib 181056 B and distal circumferential rib 181056 C of pierceable seal 181056 and causes it to translate in the proximal direction by contact with the connecting shaft. After mounting the fluid path connection to the drug container, the opening of the fluid path is basically similar to that described above.
Figure 122 shows a detailed view of the plug seal disposed within the bore of the connecting shaft. This shows a possible method of holding the plug seal in place using the 181310G tabs. These tabs control the location of the plug seal in the bore.
Figures 123-125 show additional embodiments of the disclosure illustrating alternative configurations of the plug and pierceable seal.
In the embodiment shown in Figure 126, hole 182310A is enclosed on its distal side by distal film 182350 and on its proximal side by proximal film 182352. The proximal and distal films can be constructed from any material with sufficient barrier properties to prevent the passage of foreign matter. By
228 For example, films can be constructed from a thin sheet metal material. Films can be securely attached or otherwise attached to the connecting shaft. In this way, the 182310A drill is kept in aseptic condition.
As the fluid path connection contacts the drug container, a portion of the drug container pierces, tears, or otherwise removes a portion of proximal film 182352 from the connection shaft. For example, as shown in Figure 126, a portion of the cap 182052 contacts the proximal film during installation and decouples a portion thereof from the connecting shaft. This decoupled portion of proximal seal 182352 can be retained within space 182055 formed by plug 182052 and pierceable seal 182056, thereby preventing the septic portion of proximal film 182352 from contacting the aseptic portion of pierceable seal 182056.
As also shown in Figure 126, the 182057 seal can be configured to maintain the aseptic condition of only part of the circumference of the 182056 pierceable seal. This part can be configured to align with the 182310 C opening and the piercing member 182330 after installation of fluid path connection 182300. During installation, seal 182057 is displaced by the connecting shaft as described by reference to other embodiments. Seal 182057 may be retained in position relative to the pierceable seal by coupling the seal with slot 182052D of plug 182052, proximal circumferential rib 182056B, and distal circumferential rib 182056C. During displacement, the seal can be translated into slot 182052D in the proximal direction.
Figures 127A-127D show another embodiment of a fluid path connection in which the fluid path connection includes a first rotating disk 183360 and the drug container 183050 includes a second rotating disk 183051. The first rotating disk 183360 can be configure by rotation with respect to the connecting axis 183310 about a central axis and further includes a first opening 183360A. As shown in Figure 127A, the first rotating disk may also include pole 183360B and receptacle 183360C. The second rotating disk 183051 can include complementary features to allow alignment of the first opening 183360A with the second opening 183051 A. The second rotating disk 183051 can be configured for rotation with respect to the drug container and have a second opening 183051A. One or both openings may initially be covered with a film such that the film prevents foreign material from entering the openings.
As seen in Figure 127C, during installation the first and second rotating discs are brought into contact in such a way that the first and second openings are aligned. Rotating discs can be attached using an adhesive or, alternatively,
229 They can be kept in contact by features such as the quick release arms that have been described above with respect to other embodiments. Once connected, the discs can be rotated such that they align with the chimney 183053 and the third opening 183310F on the connecting shaft 183310. Chimney 183053 can be adapted for axial movement in the distal direction, such as by a spring or other matching member capable of storing energy. As shown in Figure 127D, after alignment with the first and second openings, the stack is moved in the distal direction, passing through both the first and second openings. The chimney may have a passage through which allows the contents to flow from the drug container. In this way, a sterile fluid path is created between the drug container and the fluid path connection. The fluid path connection may further include a piercing member that is configured to, upon activation by a user, pass through the stack and pierce a pierceable seal of the drug container. After the pierceable seal is punctured, the drug fluid can pass through the piercing member and be delivered to the patient. The piercing member can be coupled with the retainer 183320. The retainer can also be configured for connection of sterile fluid line 30 (see Figure 1B) at line connection 183320A. The translation of the piercing member can be caused by the translation of the retainer.
In at least one embodiment, the present disclosure provides a user initiated fluid path connection. The fluid path connection includes: a connection shaft, a piercing member, a piercing member retainer, and a drug container having a stopper, a pierceable seal, and a barrel, where the piercing member is at least partially disposed in a sterile chamber defined by the connection axis. The fluid path connection is configured such that it can be connected to the drug container while maintaining the aseptic conditions of the fluid path. The drug container may contain a drug fluid for your minister. The fluid path connection may further be in fluid communication with a conduit that provides a fluid path for delivery of the fluid drug to the patient. After initiation by the user, the fluid drug is delivered via the fluid path to the user's body. The pierceable seal includes a seal barrier that can be penetrated, after user initiation, by the piercing member.
In another embodiment, the present disclosure provides a drug delivery pump with integrated sterility maintenance features having a housing and a mounting platform, on which an action mechanism, a fluid path connection, a power and control system, and an action mechanism having a drug container, said fluid path connection including a connecting shaft, a
230 piercing member, a piercing member retainer, and a drug container having a stopper, a pierceable seal, and a barrel, where the pierceable member is at least partially disposed in a sterile chamber defined by the connecting axis. The fluid path connection is configured such that it can be connected to the drug container while maintaining the aseptic conditions of the fluid path. The drug container may contain a drug fluid for delivery. The fluid path connection may further be in fluid communication with a conduit that provides a fluid path for delivery of the fluid drug to the patient. After initiation by the user, the fluid drug is delivered through the fluid path connection to the user's body. The pierceable seal includes a seal barrier that can be penetrated, after user initiation, by the piercing member.
XIX. Further Embodiments Regarding Skin Bonding
At least some of the drug delivery devices described in the present application, including at least those described in connection with Figures 1-127D, can be configured to incorporate the adhesive embodiments described below in connection with Figures 128A-129D.
The present embodiments disclose adhesives that have bonding forces that are sensitive to the presence of a stimulant. The adhesive can be used to adhere the drug delivery device to a patient's skin. The introduction of a stimulus can cause the bonding strength of the adhesive to decrease so that the device can be more easily removed from the patient's skin as well as possibly reducing the patient's pain or discomfort due to removal. The stimulus can be selected from any of the stimulus group that is capable of decreasing the strength of the bond including: light, such as UV light, heat, and electricity. The stimulating source can be integrated into the medical device or, alternatively, it can be independent of the medical device. Mounting and usage methods are also described.
As seen in Figures 128A-128 C, the drug delivery device 19010 may include a 19001 body, a 19002 stimulator source, a first adhesive patch 19003, and a second adhesive patch 19004. Body 19001 may include or enclose the stimulating source 2 or alternatively the stimulating source 19002 may be located outside the body 19001. The stimulating source has an inactive state and an active state. In the inactive state, the stimulating source does not produce or emit any stimuli. In the active state, the stimulating source produces and emits a stimulus. The bonding strength of the first adhesive 19003 can be such that it does not decrease in response to activation of the stimulant source 19002. The first adhesive can retain the second adhesive along with the medical device. The bond strength of the second adhesive 19004 may initially have
231 a first bonding force in the absence of a stimulus and a second bonding force in the presence of a stimulus. The 190010 device may optionally include a removable adhesive cover that protects and isolates the adhesive during transportation and prior to application of the medical device to the patient.
Before the start of drug delivery, the patient or a medical practitioner may remove the adhesive cover, if equipped. The medical device can then be secured to the patient using the adhesive. The first bonding force of the second adhesive can be such that it securely bonds the device to the patient's skin, preventing unintended removal. After delivery of the drug, or at any other desired time, the stimulant source 19002 can be activated. The activation may occur automatically upon completion of the delivery of the drug or may occur in response to patient input. For example, the device may include a stimulating action mechanism such as a button, switch, or other mechanism known to the person skilled in the art. Activation of the stimulant source causes the bonding force of at least a portion of the second adhesive patch 19004 to decrease to the second bonding force. In at least one embodiment, the bond strength of the outer perimeter of the second bond can be decreased to the second bond strength, thereby allowing the user to easily engage the edge of the bond and thereby remove or peel off the rest of the bond of the patient's skin. In these embodiments, a stimulating source can be arranged around the outer profile of the device, controlling the position of the stimulating source and the intensity of the stimulant the part of the second adhesive that is affected. In other embodiments, the bonding strength of substantially the entirety of the second adhesive decreases, thereby allowing easy removal of the device from the patient's skin. The bond strength of the second adhesive need not decrease uniformly in response to activation of the stimulant source. In other words, the bond strength of a certain part of the second adhesive may decrease to a greater degree than other parts. The cohesive properties of the adhesive can be completely removed or, alternatively, can retain some bond strength. For example, the bond strength of the adhesive, in the presence of the activated stimulant, may be sufficient to maintain its adhesion to the patient's skin until a removal operation is performed by the patient.
The stimulant can be a UV light source and be an integral aspect of the device as seen in Figures 128A-128C. The UV light source can be located at the bottom of the device in such a way that it is in proximity to the adhesive patch. The UV light source may be in electronic communication with one or more other aspects of the device in such a way that activation of the UV light source can be carried out and / or controlled by a PCB or other type of electronic controller. Activation by
232 electronic controller, can be produced in response to the end of the delivery of a drug to the patient. Activation can also be triggered by a patient input, such as the push of a button.
In other embodiments, shown in Figures 129A-129D, the stimulator source 190015 is an external stimulator source (i.e., not physically connected to the medical device). In these embodiments, the stimulant source can be delivered, with the drug delivery device 19020, to the user or can be delivered separately. The external stimulating source can be used multiple times and for multiple devices. To facilitate application of the stimulant to the adhesive, one or more aspects of the body of the device may be at least partially translucent, whereby a stimulant such as UV light is allowed to pass through. In at least one embodiment, the medical device may have a removable portion 190011. Removal of this portion of the medical device may expose a translucent portion 190012. The translucent portion 190012 may be a thin portion of the device whereby the stimulating source is allowed to be in close proximity to the adhesive. A first adhesive 190013 can be attached to the translucent portion 190012. The bond strength of the first adhesive may not be affected by the presence of the stimulant. A second adhesive 190014 can be applied, the bond strength of which is altered by the presence of a stimulant as described above. The external stimulus can be in the form of a portable UV light source in such a way that the user can direct the light source towards the adhesive.
In another aspect of the invention, the secondary adhesive may be reusable. Removal of the stimulant may allow the adhesive to return to its first bond strength. After returning to the first bonding force the device can be reapplied to the patient's skin. This can be useful in reusable medical device applications.
In applications where the bond strength of the adhesive is affected by light, the adhesive can be configured in such a way that it responds only to light of certain wavelengths. This can allow filters to be applied to prevent an unintended decrease in bond strength.
The bond strength of the adhesive can be decreased immediately in the presence of the stimulant. Alternatively, the adhesive may need to be exposed to the stimulus over an extended period of time in order to decrease the bond strength. The time can be as short as a few seconds to as long as a few minutes.
In other embodiments, a method of use is provided. The method of use may include the steps of: applying a medical device to a patient's skin using an adhesive; start the operation of the medical device; activate a stimulating source to decrease the bond strength of at least part of the adhesive; and removing the medical device from the patient. The fountain
233 Stimulant can be integrated into the medical device or can be device independent. The method may also optionally include the step of removing a cover from the adhesive patch. The method may also include removing one or more parts of the medical device from one or more other parts of the medical device.
In still other embodiments, a mounting method is provided. The mounting method may include the steps of: applying a first adhesive to a part of the medical device; applying a second adhesive at least partially to the second adhesive. The mounting method may further include mounting a stimulating source on the medical device. XX. Additional Embodiments of the Fluid Path Connector
At least some of the drug delivery devices that are described in the present application, including at least those that are described in relation to Figures 1-56, 74-129, can be configured to incorporate the embodiments of the route connector of fluid described later in relation to Figures 130-136B. The embodiments of the connected fluid path described below in relation to Figures 130-136B can be used to replace, in whole or in part, the fluid path connector 300 described above, the fluid path connector 622, the connector Fluid path 722, Fluid path connector 922, Fluid path connector 1122, Fluid path connector 2300, or any other Fluid path connector described herein, where appropriate.
In general, the present embodiments relate to fluid restriction mechanisms that control the rate of drug delivery by providing resistance and / or increasing the length of the fluid delivery path from the drug container to the needle insertion mechanism, for the supply of drug to the patient's interior. Furthermore, the fluid restriction mechanisms of the present disclosure can be easily replaced, configured, and / or stacked to provide a variety of fluid pathways and to meet a myriad of drug delivery needs. For example, the manufacturer, the drug shipper, the assembler, or another member of the production process may select and insert the fluid restriction mechanism necessary to satisfy the desired drug delivery profile. This selection and insertion can be accomplished by locating or initially replacing the fluid restriction mechanism. In addition, or alternatively, this can be accomplished by adjusting the fluid restriction mechanism, such as by rotating a configurable fluid restriction mechanism that has a plurality of fluid path channels or an individual path with conduits that are They can open or close to modify the fluid path before mounting. In addition, or alternatively, the fluid supply profile can be satisfied using a multitude of fluid restriction mechanisms, at least in part, in a series configuration or in a parallel configuration.
234
Each of these variations of the fluid restriction mechanism can be used to satisfy the desired fluid delivery profile from the drug delivery device.
Furthermore, the fluid restriction mechanisms of the present embodiments may include permeable membranes that allow the purging of gaseous fluids from the fluid path. Pump-type drug delivery systems including such fluid path systems and fluid restriction mechanisms are capable of priming to reduce or remove gaseous fluids from the fluid path system prior to the introduction of a liquid fluid to a patient . When supplying fluid subcutaneously it is important to minimize or eliminate the amount of gaseous fluid being supplied to the patient. The supply of gaseous fluids, such as air or inert gases, correlates with an increase in patients' perception of pain and can adversely affect the absorption profiles of pharmaceutical treatments. Thus, it is important to minimize or eliminate such gaseous fluids from the system prior to injection of the drug. Fluid restriction mechanisms can also be easily configured to allow fabrication of one type of mechanism (eg, plate, chip, etc.) while allowing customization of the fluid restriction mechanism before or during assembly to allow a variety of fluid restriction parameters.
As described in more detail below, an individual restriction mechanism can have a variety of selectable fluid routes or channels with different restriction parameters. Based on the desired fluid flow characteristics, the manufacturer or assembler can select the appropriate fluid path and mount the components in such a way that the desired fluid path is used. Similarly, fluid paths can be opened or closed by the assembler / manufacturer to allow for shorter or longer fluid paths, as desired to meet particular flow characteristics. Although there are important and desirable features of drug delivery devices, such features should not be cumbersome or complicated for the user. The present disclosure provides a system that enables the configurability of fluid restriction mechanisms and also the reduction or elimination of gaseous fluids from the fluid path, but which is also easy to use for clinicians and patients.
When supplying a fluid subcutaneously it is important to control or restrict the flow of fluid that is delivered to the patient. A drug delivery device, such as an infusion pump or bolus injector, may be necessary to deliver a particular amount of drug fluid over a period of time. However, the flow of drug fluid may need to be restricted as it passes through the system from the drug container to the needle insertion mechanism and to the patient. Some drug delivery device systems may use one or more active fluid restriction mechanisms,
235 one or more passive fluid restriction mechanisms, or a combination of both. The present disclosure provides configurable fluid restriction mechanisms (eg, plates, chips, etc.) for microfluidic routes that can be easily integrated into a pump-type delivery device in the fluid route between the drug container and the mechanism. needle insertion.
Pump-type delivery devices can be connected in fluid flow communication to a patient or user, for example, through a suitable hollow tubing. The hollow tubing can be connected to a hollow needle that is designed to pierce the patient's skin and to supply a fluid medium through it. Alternatively, the hollow tubing can be connected directly to the patient such as through a cannula, or the like. As an additional option, a solid drill needle can be used to pierce the patient's skin and place a hollow cannula in the proper delivery position, with the solid drill needle withdrawn or retracted prior to drug delivery to the patient. As noted above, fluid can be introduced into the body through numerous means, including, but not limited to: an automatically inserted needle, cannula, microneedle assembly, or tubing from an infusion set. Fluid flow can be initiated by a variety of different mechanisms of action that push a plunger seal into a drug container, thereby forcing the drug fluid out of the drug container. In at least one embodiment, the action mechanism can be a spring based action mechanism that uses one or more springs to drive or push the plunger seal. Actuation of the action mechanism and pressure of the plunger seal may occur before or after the fluid connection is completed, or it may cause a fluid connection to be established first before forcing the fluid through of the fluid connection. Once the fluid flow is started, the fluid restriction mechanisms of the present disclosure can be used to control the duration of the fluid flow through the drug delivery device. The fluid restriction mechanism can be located between the drug container and the fluid passage leading to the insertion mechanism, or at one or more locations in the fluid path from the drug container to the patient through the insertion mechanism. .
In a first embodiment, the present disclosure provides a selectively replaceable fluid restriction mechanism for a drug delivery device. The fluid restriction mechanism includes an opening that resides adjacent to a fluid path connection and is configured to allow the flow of a drug fluid through the opening when the fluid path connection is opened; an entry point of a fluid channel configured in such a way that the drug fluid flow can travel through the opening to the entry point and through the fluid channel to an exit point; and one
236 outlet opening of a port through which the drug fluid flow can travel after leaving the outlet point, where a fluid line is connected to the fluid restriction mechanism in the outlet opening. The selectively replaceable fluid restriction mechanism may further include a bleed opening to purge air or gases from the proximal side of the fluid restriction mechanism to a distal side of the fluid restriction mechanism; and a membrane to facilitate the passage of air or gas in one direction while preventing the passage of fluid through it. The membrane can be a permeable membrane.
In another embodiment, the present disclosure provides a configurable fluid restriction mechanism for a drug delivery device that includes an opening that resides adjacent to a fluid path connection and is configured to allow the flow of a drug fluid through opening when fluid path connection is opened; an entry point configured in such a way that the flow of the drug fluid can travel through the opening to the entry point; a plurality of fluid channels, selectable to align with the inlet and outlet point of the fluid restriction mechanism; and a port outlet opening through which the drug fluid flow can travel after leaving the outlet point, where a fluid line is connected to the fluid restriction mechanism at the outlet opening. The configurable fluid restriction mechanism can include a bleed opening to purge air or gases from a proximal side of the fluid restriction mechanism to a distal side of the fluid restriction mechanism; and a membrane to facilitate the passage of air or gas in one direction while preventing the passage of fluid through it. The plurality of fluid channels can vary in length to provide different travel durations for drug fluid flow, and / or the plurality of fluid channels can vary in diameter to provide different fluid constraints to drug fluid flow.
In at least one embodiment, a plurality of the configurable fluid restriction mechanisms can be connected in series in a stacked configuration, and where the opening of the first fluid restriction mechanism resides adjacent to a flow path connection and is configured to allow the flow of a drug fluid through the opening when the fluid path connection is opened, and the fluid conduit connects to the outlet opening of the last fluid restriction mechanism in the stacked configuration. In another embodiment, the one or more fluid channels can be selectively opened to allow drug fluid flow, and / or selectively closed to prevent drug fluid flow. In at least one embodiment, one or more fluid channels can be connected together to increase the duration of the journey that drug fluid must pass. Fluid restriction mechanisms can be in the form of a disk, a spheroid, a square, a sphere, a cube, a rectangle, or a
237 pyramid.
In yet another embodiment, the present disclosure provides a drug delivery device with a fluid delivery control including a housing, within which an activation mechanism, an insertion mechanism, a drug container having a plunger seal, and one or more of the fluid restriction mechanisms described above, where the drug container is connected at one end to an action mechanism and at another end to a fluid path connection, and the fluid restriction mechanism is connected at one end to the fluid path connection and on the other end to a fluid line, and the fluid line connects at one end to the insertion mechanism; in such a way that the fluid restriction mechanism is configured to restrict or control the flow of a drug fluid from the drug container to the insertion mechanism. The fluid restriction mechanism can be a component of the fluid path connection mounted and integrated into the barrel of a drug container, or the fluid restriction mechanism can be a component adjacent to the fluid path connection and configured to restrict the flow of drug fluid from the barrel of a drug container through the drug delivery device once the fluid path connection is opened. Alternatively, the restriction mechanism can be connected to the fluid path connection by a first fluid line, and the fluid restriction mechanism is connected to the insertion mechanism by a second fluid line, in such a way that it is restricted the flow of drug fluid between the drug container and the insertion mechanism by the fluid restriction mechanism.
Now referring to FIG. 130, an embodiment of a fluid restriction mechanism 20500 implemented in drug delivery device 10 is illustrated. As described above, the drug delivery device 10 can be used to administer the delivery of a drug treatment to the body of a user. Drug delivery device 10 includes pump housing 12. The pump casing 12 may include one or more casing subcomponents that can be fixedly coupled to facilitate easier manufacture, assembly, and operation of the drug delivery device 10. For example, the pump casing 12 may include the upper casing 12A and the lower casing 12B. Drug delivery device 10 may further include activation mechanism 14, status indicator 16, and window 18. Window 18 can be any translucent or transmitting surface through which the operation of the drug delivery device can be seen. As shown in Figure 130, the drug delivery device 10 further includes the mounting platform 20, the sterile fluid line 30, the mechanism of action 100 having the drug container 50, the insertion mechanism 200, the fluid path connection 300, and power and control system 400. 20500 mechanism
238 restriction fluid can be connected to the sterile fluid line 30, preferably, between the fluid path connection 300 and the insertion mechanism 200. One or more of the components of such drug delivery devices may be modular in that, for example, they can be preassembled as separate components and configured in place on the mounting platform 20 of the drug delivery device 10 during manufacture. .
The fluid restriction mechanisms of the present disclosure can take a variety of configurations while remaining within the scope of the claimed embodiments herein. Fluid restriction mechanisms provide a means of controlling fluid supply, by restricting fluid path flow and / or by increasing the length of the fluid path the fluid must travel between the fluid container and the insertion mechanism before delivery to the patient. The fluid restriction mechanisms of the present disclosure can be easily replaced, configured, and / or stacked to allow the drug delivery device to meet the desired drug delivery profile (eg, duration of delivery). Fluid restriction mechanism 20500 can be connected to sterile fluid conduit 30, preferably between fluid path connection 300 and insertion mechanism 200. For example, fluid restriction mechanism 20500 can be connected to the beginning of fluid line 30 (between fluid path connection 300 and fluid line 30), to the end of fluid line 30 (between fluid line 30 fluid and insertion mechanism 200), or anywhere in between along fluid line 30.
Fluid restriction mechanism 20500 resides within the housing of the drug delivery device, as shown in Figure 130. Figure 131A shows an isometric view of a fluid restriction mechanism, according to at least one embodiment of the present disclosure, attached to an integrated sterile fluid path connection and a drug container. In such an embodiment, the fluid restriction mechanism can be a component of the integrated sterile fluid path connection and drug container. As shown in Figure 131B, the fluid restriction mechanism can be attached to a sterile fluid path connection and a drug container, such as by retaining through a plug 52 which can be a plug that engages the barrel 58 . In this configuration, the fluid restriction mechanism may include a piercing member 20510, such as a needle, that is capable of piercing a seal 56 of the sterile fluid path connection 300 to allow fluid flow from chamber 21 of drug from barrel 58 of drug container 50. In this configuration, the seal 56 is caused to slide upward, and to be pierced by the piercing member 510 after hydraulic and / or pneumatic pressure of the fluid within the drug chamber 21 which is caused by the acting action mechanism 100 over seal 60
239 piston. Once the sterile fluid path connection 300 is opened, the drug fluid can travel through piercing member 510, through the fluid channel (s) of fluid restriction mechanism 20500, out through port 20512 to through fluid line 30 to insertion mechanism 200 for drug delivery to the patient. Figure 131C shows a side view of the fluid restriction mechanism shown in Figure 131 A. As will be further detailed herein, the fluid restriction mechanism 20500 may also include a membrane 20309, such as a partially permeable membrane, that is capable of purging air or other gas from the sterile cavity between the 20500 restriction mechanism. fluid and seal 56. In such a configuration, the fluid restriction mechanism 20500 need not move or move once mounted to the barrel 58 of the drug container 50 as the integrated sterile fluid path connection 300 occurs in the drug container 50. This configuration of the fluid restriction mechanism may be preferred for use with the integrated fluid path connection and drug container described in International Patent Application Document No. PCT / US2013 / 030478, which is incorporated to this document by reference in its entirety.
Figure 132A shows an isometric view of a fluid restriction mechanism, in accordance with another embodiment of the present disclosure. In this configuration, the fluid restriction mechanism 201500 is attached to a sterile fluid path connection that may or may not be integrated into the drug container. In this configuration, seal 56 can be held in place at the distal end of barrel 58 by plug 52, and sterile fluid path connection 300 can be external (i.e., not integrated) to barrel 58 of container 50 of drug. This configuration of the fluid restriction mechanism may be preferred for use with the fluid path connection and the drug container described in International Patent Application document No. PCT / US2012 / 054861, which is incorporated in the this document by reference in its entirety. The fluid restriction mechanism 201500 of this embodiment can be attached to the distal end of the sterile fluid path connection 300 which is capable of acting upon and piercing the seal 56 retained in the barrel 58 of the drug container 50. In that embodiment, piercing member 201510 would be in place of a conduit or port connected to the distal surface of the fluid path connection. Alternatively, a piercing member 201510 can be used in this embodiment to function as part of the integrated fluid path connection and drug container, and to pierce seal 56 to allow drug flow from drug container 50. Figure 132B shows an exploded isometric view of the fluid restriction mechanism, and the connection of the sterile fluid path and the drug container, shown in Figure 132A. Figure 132C shows a side view of the fluid restriction mechanism shown in Figure 132A.
Figure 133A shows an exploded isometric view of the restriction mechanism.
240 of fluid shown in Figures 131A-131C. Although the following description provides details with reference to the embodiments shown in Figures 131A-131C, the description with reference to the function of the fluid restriction mechanism can also provide details to the embodiments shown in Figures 132A-132C. . Figure 4A shows fluid restriction mechanism 20500 in the form of two separate components. Figure 133B shows another angle of the exploded isometric view of the fluid restriction mechanism shown in Figure 133A. As would be understood by one of ordinary skill in the art, this is primarily for ease of manufacture and the 20500 mechanism can be a single unified component if manufactured, for example, by injection molding or other suitable means. In this two-part assembly the fluid channel or channels can be imparted, such as by carving or other suitable manufacturing means, into the first component 20500B of the fluid restriction mechanism and then closed by attachment to a second component 20500A. The two components can be held and held together by quick release arms, adhesives, etc., or other mechanisms that are easily known in the industry to provide a tight seal to the fluid channel or channels of the fluid restriction mechanism. The second component (eg, cover plate) 20500A can be cast, molded, or otherwise connected to the first component (eg, restriction plate) 20500B. The fluid path of each of the fluid channels can be adjusted in thickness, length, curvature of the path, and any number of tortuous path parameters, for example, to produce a fluid restriction of any desired range. The path that a drug fluid can travel through fluid restriction mechanism 20500 is shown with reference to Figure 133C, which provides a cross-sectional view of the fluid restriction mechanism shown in Figures 133A-133B. Drug fluid can enter fluid restriction mechanism 20500 through opening 20520A of piercing member 510. The drug fluid then enters the fluid channel or channels at inlet point 20520B. Drug fluid is retained in fluid channel (s) 20520C by the tight seal provided by pairing the second component 20500A to the first component 20500B.
In the shown embodiment, the fluid channel (s) are spirally shaped to lengthen the length of the path the fluid must pass (ie, prolonging the time or duration of drug delivery). The width of the channel or channels can also be modified and used to control the flow parameters through the fluid restriction mechanism. Drug fluid then travels through fluid channel (s) 20502C to outlet point 20520D, at which point drug fluid is traveled through outlet opening 20514 or port 20512 to conduit 30 of fluid (visible in Figures 131A-131C). The fluid channel (s) can be shortened or lengthened to provide the
241 desired duration of fluid delivery time (ie, the drug fluid can be traveled a longer route or a shorter route through the fluid restriction mechanism). In addition, or alternatively, the fluid channel (s) can restrict the fluid flow of drug by operating as an orifice. As would be easily understandable to the person of ordinary skill in the relevant art, the flow of fluid in a tube or conduit is always accompanied by the friction of the fluid particles rubbing against each other and, therefore, by the loss of energy available to job. In other words, there must be a pressure drop in the flow direction. Therefore, the fluid channel or channels of the fluid restriction mechanism can function as an orifice for metering the flow rate, for flow restriction and / or to reduce pressure. For liquid flow, multiple orifices are sometimes used to reduce pressure in stages in a way that cavitation is avoided. Simultaneously, a purge opening 20530A, 20530B can be used to purge air or gas from the proximal side of fluid restriction mechanism 20500 to the distal side of fluid restriction mechanism 20500. A membrane 20309, such as a partially permeable membrane, may be used, for example, to facilitate the passage of gas (eg, air) in one direction while preventing the passage of fluid therethrough.
Figures 134A-134B show a configurable fluid restriction mechanism, according to another embodiment of the present disclosure, in exploded and front views, respectively. In this embodiment, fluid restriction mechanism 20500 contains more than one fluid channel 20520C, 20521C, 20522C, and 20523C. Therefore, the same fluid restriction mechanism 20500 can be used in a variety of configurations to provide the desired fluid flow parameters. If a shorter fluid supply duration is desired, channel 20522C can be selected and aligned with input point 20520B and output point 20520D. If restrictive fluid flow is desired, channel 20523C can be selected and aligned with input point 20520B and output point 20520D. Alternatively, channels 20521C or 20520C can be selected and aligned with input point 20520B and output point 20520D to achieve the desired drug delivery parameters. This is facilitated, for example, during mounting of the device, by identifying the desired drug delivery parameters and the appropriate fluid channel, and rotating and mounting the fluid chip 20550A in the corresponding slot 20550B in such a way that the selected fluid channel aligns with inlet point 20520B and outlet point 20520D. This is shown in Figure 134B.
Any number of different channels can be provided and use this embodiment of a configurable fluid restriction mechanism. Furthermore, the desired channels can be opened or closed by removal or addition, respectively, of barriers between the channels. For example, if an even longer fluid channel is desired, the barriers between
242 channels 20521C and 20520C in such a way that fluid initially flows into channel 20520C through inlet point 20520B, then through channel 20521C, and then back through the rest of channel 20520C to point 20520D of departure. In a further embodiment, the fluid restriction plate can have a variety of sequential or parallel routes that are configurable to supply the desired fluid restriction parameters. For example, the fluid restriction plate can have a variety of different routes of different lengths and limitations, and the specifically desired fluid route can be selected during mounting to produce the desired fluid restriction for the delivery device system. drug. One or more of these routes can be '' opened '' or closed prior to mounting to allow for a variety of configurable fluid routes. Although plates are discussed and shown herein, fluid restrictors can assume a variety of different shapes and configurations and include, but are not limited to, spheres, discs, thick discs, semicircles, rectangles, cubes, pyramids, and Similar. This configurability provides even more variation to the diversity of channels or fluid path configurations that the present disclosure can employ. More complex shapes including different fluid pathways can be used, and are only restricted by economic feasibility and known manufacturing methods. For example, more complex fluid channel shapes and configurations may be possible by 3D printing, or other complex manufacturing methods. Simultaneously, a purge opening 20530A, 20530 B can be used to purge air or gas from the proximal side of fluid restriction mechanism 20500 to the distal side of fluid restriction mechanism 20500. A membrane 20309, such as a partially permeable membrane, may be used, for example, to facilitate the passage of gas (eg, air) in one direction while preventing the passage of fluid therethrough.
Figure 135A shows an isometric view of a stackable fluid restriction mechanism, in accordance with another embodiment of the present disclosure. Figure 135B shows an exploded isometric view of the stackable fluid restriction mechanism. The stackable fluid restriction mechanism can utilize any of the fluid restriction arrangements described above with reference to Figure 133A and Figure 134A, in the configurations shown in Figures 131A-131C, Figures 132A- 132C, or the other configurations described herein. Therefore, one or more fluid restriction mechanisms can be used in a stacked configuration to provide an additional distance that the drug fluid must travel to extend the duration of drug delivery. In such a stacked configuration, a spacer plate 20503B may be used between two restriction plates 25503A and 20500B, in order to align the fluid inlet and outlet points with the corresponding or adjacent plates.
243
Any number of these plates can be used to achieve the desired drug delivery parameters.
The fluid restriction mechanisms of the present disclosure are shown primarily in a disc-shaped configuration, although the shape is not a necessary limitation of the present disclosure and any number of known ways can be used. For example, Figure 136A shows an isometric view of a rectangular fluid restriction mechanism, in accordance with a further embodiment of the present disclosure. Figure 136B shows the isometric view of the fluid restriction mechanism 202500 shown in Figure 136A, with the top component of the fluid restriction mechanism removed. As shown, the fluid restriction mechanism 202500 can take any number of shapes or dimensions, provided that there is at least one fluid channel therein that has at least one inlet point and at least one outlet point. through which the drug fluid can travel. In addition, the fluid restriction mechanism 202500 can be connected to the beginning of the fluid line 30 (between the sterile fluid path connection 300 and the fluid line 30), to the end of the fluid line 30 (between the fluid line 30 fluid and insertion mechanism 200), or anywhere in between along fluid line 30 (as shown in Figures 136A-136B).
The assembly and / or fabrication of the above-described embodiments of the fluid restriction mechanism, drug delivery pump 10, or any of the individual components can utilize a variety of materials and methodologies known in the art. For example, a variety of known cleaning fluids such as isopropyl alcohol and hexane can be used to clean components and / or devices. Similarly, a variety of known adhesives or glues can be employed in the manufacturing process. In addition, siliconization and / or lubrication fluids and processes can be used during the manufacture of the new components and devices. In addition, known sterilization processes can be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
A fluid path connection, and specifically a sterile sleeve of the fluid path connection, can be connected to the cap and / or pierceable seal of the drug container. The fluid restriction mechanism can be connected to the other end of the fluid path connection. A fluid line can be connected to the fluid restriction mechanism at one end and to the insertion mechanism at the other end, such that the fluid path, when opened, connected, or otherwise enabled, travels directly from the drug container, the fluid path connection, the fluid restriction mechanism, the fluid passage, the insertion mechanism, and through the cannula for delivery of drug to a user's body. As described above, the fluid restriction mechanism is
244 you can alternatively locate between the sterile path connection and the insertion mechanism in such a way that a first fluid line is directly connected to the sterile path connection and fluid restriction mechanism, and then a second fluid line is connected to the fluid restriction mechanism and insertion mechanism. Regardless of the configuration, or the order of the components, the fluid path, when opened, connected, or otherwise enabled, travels directly from the drug container, the fluid path connection, the fluid restriction mechanism, the fluid conduit, the insertion mechanism, and through the cannula for delivery to a user's body. The components that make up the path for fluid flow are now assembled. These components can be sterilized, by a variety of known methods, and then fixedly or removably mounted to a mounting platform or housing of the drug delivery device, as shown in Figure 130.
XXI. Additional Embodiment Mechanism Embodiments
At least some of the drug delivery devices described in the present application, including at least those described in connection with Figures 1-56, 74-136B, can be configured to incorporate embodiments of the insertion mechanism that they are described later in relation to Figures 137A-139C. The embodiments of the insertion mechanism described below in relation to Figures 137A139C can be used to replace, in whole or in part, the insertion mechanism 200, the insertion mechanism 2000, the insertion mechanism 17200, the insertion mechanism 172200 insertion described above, or any other insertion mechanism described herein, where appropriate.
When supplying drug fluid to a user, such as by subcutaneous or intramuscular injection, it is important to minimize or eliminate the amount of gaseous fluid that is supplied to the user. The supply of gaseous fluids, such as air or inert gases, correlates with an increase in pain perception by patients and can adversely affect the absorption profiles of pharmaceutical treatments. As such, it is important to either remove such gaseous fluids from the system prior to injection of the drug. Although this is an important and desirable feature of drug delivery devices, such features should not be cumbersome or complicated for the user. The present embodiments provide a system that allows the reduction or removal of gaseous fluids from the fluid path, but is still easy to use for clinicians and patients.
More particularly, the present embodiments provide insertion mechanisms that have purged fluid pathways, and pump-type drug delivery systems that include such purged fluid pathways that are capable of priming to reduce or
245 removing gaseous fluids from the fluid path system prior to the introduction of a liquid fluid to a user. The present embodiments relate to purged fluid path systems having a membrane, such as a permeable or semipermeable membrane, and drug delivery pumps that use such purged fluid path systems for parenteral delivery of drug fluids. Such new components and devices provide a mechanism for priming (eg, evacuation or removal of air or other gaseous fluid) of the fluid pathway prior to injection and dosing of the drug treatment. The new systems and devices of the present disclosure can be employed in a variety of different configurations, and can be used with both pre-load cartridges and primary-load drug containers at the time of use.
In at least one embodiment, the present disclosure provides an insertion mechanism having a purged fluid path including: one or more insert matching members, a shaft, a needle, a refraction matching member, and a manifold having a septum, a cannula, a manifold inlet, and a membrane, where the annular space within the manifold between the septum, the cannula, the inlet of the manifold, and the membrane defines a header of the manifold, where the manifold is configured to purge a gaseous fluid through the membrane and fill with a liquid fluid for delivery to the user through the cannula. The collector inlet can be connected to a fluid line. The insertion mechanism can be configured to be mounted internally within a drug pump or externally attached to a drug pump via a conduit. In at least one embodiment, the purged or purgable insertion mechanism comprises two insert matching members. The septum closes the top of the collector while allowing the needle to pass through it. Another collector opening is at least temporarily blocked by the needle as it resides within the cannula and / or other occlusion element such as a ferrule or plug, prior to operation of the insertion mechanism. The manifold inlet receives fluid flow from the fluid line. The only remaining collector opening is blocked by a membrane until the injection mechanism operates.
The membrane can be a variety of filtration membranes that are capable of allowing the passage of gaseous fluids but prohibit the passage of liquid fluids. For example, the membrane can be a permeable membrane or a semipermeable membrane. Furthermore, the membrane can be or function as a sterile barrier. In at least one embodiment, the membrane is a permeable membrane selected from the group consisting of polyethylene terephthalate (PET), polytetrafluoroethylene (PTFE), one or more styrenes, and polyethylene fibers, and the combination thereof. The membrane can be a separate component or be an integrated part, such as part of the wall, of the collector.
The insertion mechanism that has a purged fluid path may further include
246 a sensor. The sensor may be any number of sensors known to the person skilled in the art, such as those selected from the group consisting of pressure sensors, fluid sensors, optical sensors, mechanical sensors, electrical sensors, and electromechanical sensors, and combinations thereof.
In another embodiment, the present disclosure provides a drug delivery pump including a housing and a mounting platform, on which an activation mechanism, an action mechanism, a fluid path connection, a delivery system can be mounted. energy and control, and an insertion mechanism that has a purged fluid path. The insertion mechanism that has a purged fluid path can be as described above. In a preferred embodiment, the drug pump uses a purged or purgeable insertion mechanism that has a purged fluid path that includes: one or more insert matching members, a shaft, a needle, a refraction matching member, and a manifold having a septum, a cannula, a manifold inlet, and a membrane, where the annular space within the manifold between the septum, cannula, manifold inlet, and membrane define a manifold header, where the manifold is configured to purge a gaseous fluid through the membrane and fill with a liquid fluid for delivery to the user through the cannula. The collector inlet can be connected to a fluid line. The insertion mechanism can be configured to be mounted internally within a drug pump or externally attached to a drug pump via a conduit. In at least one embodiment, the purged or purgable insertion mechanism comprises two insert matching members.
In yet another embodiment of the present disclosure, a method of operating the insertion mechanism having a purged fluid path includes the steps of: (i) initially holding a needle in a first position where fluid passage from a head is blocked from a collector to a collector through the cannula; (I) activating the flow of liquid drug fluid from a drug container through a fluid line in the collector header of the collector; (iii) purging a gaseous fluid through a membrane into the manifold while prohibiting the passage of the liquid drug fluid through the membrane; (iv) activating an insertion matching member to move the needle and cannula from the first position to a second position within the body of a user; and (v) activating the retraction matching member to move the needle from the second position to the third position, where the third position allows the liquid drug fluid to pass from the collector header to the collector through the cannula and into the inside the user's body. In at least one embodiment, the step of activating an insertion matching member to move the needle and cannula from the first position to a second position occurs after the step of purging a gaseous fluid through a membrane into the manifold. . In another embodiment,
247 The step of activating an insertion fitting member to move the needle and cannula from the first position to a second position may occur prior to the step of purging a gaseous fluid through a membrane into the manifold in such a way that purging through the membrane is allowed only once the needle is in the second position. In such an embodiment, the step of activating an insert suiting member to move the needle and cannula from the first position to a second position can cause a covering element to be removed from the outside of the collector membrane to allow purging of any gaseous fluid from the fluid path. The covering element may be, for example, a cover, sleeve, or sleeve. However, in either embodiment, the passage of the liquid drug fluid is allowed to occur only after the purge step and after translation of the needle from the second position to the third position, where the third position allows the passage of the liquid drug fluid from the collector header of the manifold through the cannula and into the patient's body. In yet another embodiment, the method further includes, prior to the step of activating a retraction adequacy member to move the needle from the second position to a third position, the step of: measuring with a sensor the substantial completion of the purge of gaseous fluid through the membrane.
Turning to the figures, the pump-type drug delivery devices of the present disclosure can be connected in fluid flow communication to a patient or user, for example, through any suitable hollow tubing. A solid drill needle can be used to pierce the patient's skin and place a hollow cannula in the proper delivery position, with the solid drill needle withdrawn or retracted prior to drug delivery to the patient. As noted above, fluid can be introduced into the body through any number of means, including, but not limited to: an automatically inserted needle, cannula, microneedle assembly, or tubing from an infusion set . A variety of mechanisms can also be employed to activate insertion of the needle into the patient. For example, a single spring insertion mechanism (as shown in Figure 7A) or a double spring insertion mechanism (as shown in Figure 7B) can be employed to provide sufficient force to cause the needle to the cannula pierce the patient's skin. The same spring, additional spring, or other similar mechanism can be used to retract the patient's needle. In at least one embodiment, the insertion mechanism can generally be as described in International Patent Application document No. PCT / US2012 / 53174, which is hereby incorporated by reference herein in its entirety. Such a configuration can be used for insertion of the drug delivery path to, or below, the patient's skin (or muscle) in a manner that minimizes pain in the patient. Other known means can be used for insertion of a fluid route and are contemplated within the limits of the
248 present invention.
In a first embodiment, the present disclosure provides a fluid routing system that allows a tube, duct, or other fluid channel to be evacuated of air (or other gaseous fluid) prior to operation. In one such embodiment, the purgeable fluid path system is integrated into an insertion mechanism 200. The insert mechanism includes an insert mechanism housing 202 having one or more closing windows 202A, a base 252, and a sterile liner 250, as shown in Figure 8A. Base 252 can be connected to mounting platform 20 to integrate the insertion mechanism into drug delivery pump 10 (as shown in Figure 1B). The connection of the base 252 to the mounting platform 20 can be, for example, in such a way that a hole is allowed to pass through the bottom of the base to the mounting platform allowing direct contact of the base with the user's body. In such configurations, the bottom of the base 252 can include a sealing membrane 254 that, in at least one embodiment, can be removed prior to use of the drug delivery pump 10. Alternatively, the sealing membrane 254 may remain attached to the bottom of the base 252 in such a way that needle 214 pierces the sealing membrane 254 during the operation of the drug delivery pump 10. As shown in Figures 8A and 8B, the insertion mechanism 200 may further include an insert fit member 210, a shaft 212, a needle 214, a retract fit member 216, a clip 218, a guide 220 collector, a septum 230, a cannula 234, and a collector 240. Collector 240 can be connected to fluid conduit 30 to allow fluid flow through collector 240, cannula 234, and into the user's body during drug delivery, as described in greater detail below.
Manifold guide 220 may include an upper chamber 222 and a lower chamber 226 separated by a manifold guide ring 228. Upper chamber 222 may have an inner upper chamber 222A, within which retraction adequacy member 216, clip 218, and shaft 212 may reside during an initial blocked stage of operation, and an outer upper chamber 222B, which connects with insert matching adequacy member 210. In at least one embodiment, the insert fit member 210 and the refractive match member 216 are springs, preferably compression springs. Shaft 212 may be engageably connected to a proximal end of needle 21.4 in such a way that axial translational displacement of shaft 212 causes relative movement of needle 214. Figures 137A and 137B show isometric views of fluid conduit 30 connected to manifold 240 at manifold inlet 240A. Figures 137A and 137B show an embodiment of the present disclosure in which the membrane 21233 is located in a part of the collector 240 basically opposite to the collector inlet 240A; however, the membrane could be located at any number of positions within manifold 240. Septum 230 closes the
249 upper part of the collector 240 from the environment and / or the interior of the pump casing, while allowing a passage through for the needle or trocar.
As used herein, needle is intended to refer to a variety of needles including, but not limited to, conventional hollow needles, such as rigid hollow steel needles, and solid core needles more commonly called trocars. In a preferred embodiment, the needle is a 27 gauge solid core trocar and in other embodiments, the needle may be any needle of adequate size to insert the cannula for one type of drug and drug delivery (eg, subcutaneous, intramuscular , intradermal, etc.) intended. After mounting, the proximal end of needle 214 is held in fixed contact with shaft 212, while the remainder of needle 214 is allowed to pass through a retraction fit member 216, a staple opening 218, and a manifold guide 220. Needle 214 can further pass through septum 230, cannula 234, collector 240 through collector header 242, sterile liner 250, and base 252 through opening 252A in the base. Septum 230, cannula 234, and manifold 240 may reside within lower chamber 226 of manifold guide 220 and within sterile liner 250 until operation of the insertion mechanism. In this position, cannula 234 can reside on a distal portion of needle 214 and be held in place within manifold header 242 of manifold 240 by a ferrule 232. Ferrule 232 ensures that cannula 234 remains basically fixed and in sealed engagement with manifold 240, for example, to maintain sterility of manifold header 242 until device operation. As described above, ferrule 232 can also function as a restriction or occlusion element to restrict, at least partially, the flow of liquid fluid from manifold 240 through cannula 234. Similarly, septum 230 resides basically fixed and in sealed engagement with the top of manifold 240 to maintain sterility of header 242. These aspects and components may be more clearly visible in the cross-sectional view shown in Figure 138A.
As will be understood by one of ordinary skill in the art, the restriction of fluid flow from the header of the manifold to the user through the cannula can be adjusted to achieve the desired fluid flow characteristics. In at least one embodiment, fluid flow is basically completely prevented until it is desirable and allowed by removal of the restriction. However, in other embodiments, the restriction (for example, the needle, plug, or other occlusion element that prevents or reduces fluid flow) does not completely prevent fluid flow but can instead be used to reduce or dose the fluid flow through the cannula. This may be desirable, for example, when the fluid flow is initially low in volume and then increases at a later time as the operation of the device proceeds. Similarly, one or more constraints can be used or
250 occlusion elements separately or concurrently. For example, as further described herein, the ferrule can be used to restrict the flow of fluid from the manifold through the cannula to the user.
Similar to the insertion mechanism 200 described in connection with Figure 7A and Figures 8A-8B, the insertion mechanism 21200 of 138A-138F may have a purged fluid path and may use an insert fit member 210 individual. In an alternate embodiment of insertion mechanism 2121200 having a purged fluid path, as shown in Figure 7B, insertion mechanism 21200 may include two insert fit members 210A, B. Insertion mechanism 21200 further includes insertion mechanism housing 202 (shown in a transparent view), manifold guide 220, sterile liner 250, base 252, and other components similar to those described above by reference. to the insertion mechanism 21200. In the embodiment of the two insertion matching members of the insertion mechanism shown in Figure 7B, the collector guide ring includes two circular platforms on which insertion matching member 2210 A, B can be supported. Insertion mechanism 21200 can function identically to insertion mechanism 21200, but can provide additional insertion force and / or facilitate different packaging configurations through the use of multiple insert suitability members 210 A, B. The components and functions of insertion mechanisms will be further described herein with the understanding that similar or identical components may be used for insertion mechanism 21200, insertion mechanism 22200, and all reasonably understood variations thereof. . Regardless of the single or multiple configuration of the insert suitability member, the insert mechanisms of the present disclosure incorporate a purged fluid path capable of allowing priming (eg, evacuation or expulsion of gaseous fluid) from the drug container, the fluid conduit, and the manifold prior to delivery of the drug fluid to the patient. This is enabled, at least in part, by the location of membrane 21233 in manifold 240 and the function of insertion mechanism 21200 during the insertion and refraction stages of operation.
The operation of the insertion mechanism having a purged fluid path is described herein by reference to the above components, in view of Figures 138A-138F. Figure 138A shows a cross-sectional view of the insertion mechanism 21200 having a purged fluid path, according to at least one embodiment of the present disclosure, in a locked and ready-for-use stage. In this initial configuration, the insert fit member 210 and refractive match member 216 are each retained in their compressed, energized states.
251
As shown, needle 214 can pass through an opening in clip 218 and collector guide 220 in septum 230 and collector 240. Septum 230 resides within collector 240. Collector 240 further includes an inlet 240A. collector to which the fluid line 30 can be connected. This connection is such that sterility is maintained from the drug container 50 of the action mechanism 100, through the fluid path connection 300 and the fluid line 30, at the sterile collector header 242 of the collector 240 and sterile liner 250 to maintain the sterility of needle 214, cannula 234, and the fluid path to insertion into the user for drug delivery. Fluid line 30 connects the fluid path from drug container 50 (visible in Figure 1B) to insertion mechanism 21200 at manifold inlet 240A and in header 242. As described above, septum 230 closes the top of manifold 240 while needle 214 is allowed to pass through. Another opening in manifold 240 is at least temporarily blocked by needle 214 as it presides within cannula 234, and / or by another occlusion element such as ferrule 232, prior to operation of insertion mechanism 21200. The only remaining opening in manifold 240 is blocked by membrane 21233. As will be readily understood by the person skilled in the art, the 21233 membrane can be any of a variety of permeable or semi-permeable membranes that are capable of allowing the passage of gaseous fluids while prohibiting the passage through the 21233 membrane of liquid fluids. . In at least one embodiment of the present disclosure, this is accomplished using a permeable membrane, such as a hydrophobic permeable membrane, i.e. permeable to a gaseous fluid but not to a liquid fluid, such as liquid drug treatment. In at least one embodiment of the present disclosure, it may be beneficial to use a permeable membrane that is also a sterile barrier. For example, membrane 21233 may be a polymeric filter made of polyethylene terephthalate (PET) or polytetrafluoroethylene (PTFE), a variety of types of styrene, and / or a high-density polyethylene fiber (such as that marketed under the name commercial TYVEK by DuPont), among many other types of medical grade gas filtration membranes. Therefore, because the desired fluid path from manifold 240 to the user through cannula 234 is blocked by needle 214, the only available route for any gaseous fluid is through membrane 21233.
As shown in Figure 138B, when the drug pump is activated and the liquid drug fluid (shown as a framed area) is allowed to pass through the fluid line 30, any gaseous fluid in the path of Fluid enters manifold header 242 of manifold 240. Since the pressure of the liquid drug fluid continues to build up in the fluid line 30, it pushes the gaseous fluid out of the header 242 through the membrane 21233 (shown as solid arrows). How has it
252 noted above, this is possible because the fluid path to the user through cannula 234 remains blocked by needle 214. Figure 138C shows a cross-sectional view of an insertion mechanism that has a purged fluid path when the liquid drug fluid fills the manifold and the gaseous fluid is pushed substantially completely through the permeable membrane (as shown via the framed area that almost reaches the membrane 21233 and fills the header header 242 complete). Through the steps of operation of the insertion mechanism having a purged fluid path shown in Figures 138A-138C, needle 214 basically remains in a first position, for example, a locked position, within insertion mechanism 21200 . In this first position, needle 214 blocks the fluid path through cannula 234 to the user. When the drug container, fluid line 30, and manifold header 242 are purged of gaseous fluid, such as air or inert gas, the needle insertion mechanism can be unlocked and activated to move needle 214 to a second position, for example, an inserted position. Figure 138B shows a cross-sectional view of an insertion mechanism having a purged fluid path, in accordance with a first embodiment of the present disclosure, in an unlocked step and inserted with needle 214 in the second position. In this second position, needle 214 and cannula 234 are inserted (in the direction of the solid arrow in Figure 138D) into the user's body.
The timing of the activation of the insertion mechanism 21200 to move the needle 214 from the first position to the second position can be coordinated by a timing mechanism controlled, for example, by the power and control system or by a mechanical delay directly from user activation of the drug pump. In addition, or alternatively, a variety of sensors can be used to identify the time when the gaseous fluid has been essentially entirely expelled from the fluid path and the fluid path is primed for delivery of liquid drug fluid to the user. For example, pressure sensors can be used to monitor the return pressure (eg, pressure build-up) in the fluid path resulting from the liquid fluid that basically fills the manifold header 242 and the expulsion of any gaseous fluid from the drug, fluid line 30, and manifold 240. Similarly, the rate of fluid flow can be actively controlled or passively controlled. For example, in at least one embodiment of the present disclosure, pipe or other fluid lines with a diameter or geometry, orifice, or other controlled limiting mechanism can be used to control the flow rate. Such mechanisms can provide means for passive control of the supply rate. The orifice or tubing can be used to passively modulate the flow when coupled to an induced pressure in the primary drug container, i.e. the pressure exerted by the pump mechanism on the liquid fluid when forced out of the container
253 of primary drug. In some embodiments, the device can be configured to actively control the supply flow by electrical means, mechanical means, or a combination of both. For example, one or more solenoids can be used to actively control the supply flow by closing and / or opening the fluid path.
In addition, or alternatively, one or more timing mechanisms that couple directly to the action mechanism can be used that subsequently slow down or dose the delivery rate or total time to deliver a volume of liquid fluid from the primary drug container. It is to be understood that the mechanisms, methods, and devices of the present disclosure can be used to control the total drug delivery time, the static delivery rate over the total delivery time, a dynamic delivery rate during any period of total supply time interval, or any combination of the above. For example, the device can be configured to provide drug delivery that, from start to finish, completes in a specified amount of time, for example 5 minutes. This could be configured to be Independent of the supply rate, in such a way that: (a) the supply rate can be initially high and then subsequently low; (b) a constant rate during the total supply time; or (c) constant rates that vary at different intervals within the total supply time; (d) or any combination of these delivery methodologies. Insertion of the blocking needle and activation of liquid fluid flow (eg drug treatment) can be similarly controlled to ensure there is sufficient time for the system to purge (i.e. prime the fluid path) ) before the introduction of the liquid fluid to the user. After basically all of the gaseous fluid has been expelled from the drug container, the fluid line, and the manifold, and the insertion mechanism has moved the needle from the first position to the second position, the fluid path is ready to allow delivery of the drug fluid to the user.
Figure 138D shows a cross sectional view of an insertion mechanism in the second position, eg, needle inserted. As shown, sterile liner 250 is allowed to collapse when insert fit member 210 expands and inserts needle 214 and cannula 234 into the user's body. At this stage, needle 214 is inserted into the user's body to place cannula 234 in position for drug delivery. As shown in Figure 138E, after insertion of needle 214 and cannula 234 by operation of insertion matching member 210 as described above, needle 214 retracts back (i.e., is translated axially in proximal direction) in the insert mechanism housing 21200. Manifold guide 220 and clip 218 (shown in Figures 8A and 8B), and guide protrusions 204, are dimensioned such that when manifold 240 basically bottoms out at base 252, i.e.
254 reaches its full axial translation in the distal direction, the clip 218 escapes from the guide protrusions 204 and is allowed to bend outward to disengage from the shaft 212. Upon such disengagement, the retraction adequacy member 216 is allowed to expand axially in the proximal direction (ie, in the direction of the continuous arrow in Figure 138E) from its initial compressed, energized state. A suitable locking mechanism prevents axial translation in the proximal direction of the manifold guide 220 and the components of the insertion mechanism that are distal to (ie, below) the manifold guide ring 228. The expansion of the retraction fit member 216 translates the shaft 212, and the needle 214 to which it is connected, axially in the proximal direction from the second position to a third position, ie, a needle retracted position. Ferrule 232 retains cannula 234 inserted into the user's body through opening 252A in the base. After retraction of needle 214 from cannula 234, the fluid path from the manifold header 242 to the user's body through cannulas 234 is opened and fluid can begin to pass through cannula 234, as shown in Figure 138E. When the fluid path connection to the user is complete, the fluid drug treatment is forced from the drug container through the fluid path connection and the sterile fluid line at the header 242 and through the cannula 234 for delivery into the user's body. Therefore, activation of the insertion mechanism inserts needle 214 and cannula 234 into the user's body from a first position to a second position, and subsequently retracts needle 214 from the second position to a first position, i.e. the retracted position, while maintaining cannula 234 in fluid communication with the user's body. Figure 138F shows a cross-sectional view of an insertion mechanism having a purged fluid path in the third retracted position for drug delivery. As shown, needle 214 need not be fully retracted from septum 230, although this may be desirable and permissible in other embodiments of the present disclosure, as long as the fluid path through cannula 234 is opened to the user's body. At the end of drug dose delivery, cannula 234 can be removed from the user's body by removing the drug pump from contact with the user.
In another embodiment of the present disclosure, the fluid path can be blocked by a stopper, stopper, cork, or other removable occlusion element. For example, during the purge step, a removable plug or stopper can be used to block the part of the fluid path that is in connection with the user. The plug, stopper, or other similar occlusion element retracts or withdraws from the path after the purge has basically been completed, allowing the liquid fluid to be supplied to the user. This may be desirable in configurations using, for example, a rigid needle in fluid connection with the patient. For example, in at least one embodiment of the present disclosure, a needle can be used
255 rigid socket instead of the solid core trocar needle described above. In such an embodiment, the needle and, optionally, a cannula are inserted from a first position to a second position in the user. The needle and optional cannula are then retained within the user's body. Instead of retracting the needle, the needle remains in the second position and a plug, stopper, or other similar occlusion element is removed or retracted from the needle to a third position, after the purge step, to open the path of fluid for drug delivery to the user.
A method of operating an insertion mechanism having a purged fluid path in accordance with the present disclosure includes: initially holding a needle in a first position within a cannula and thereby blocking the passage of fluid from the manifold header from a collector through the cannula; activating the flow of liquid drug fluid from a drug container through a fluid line to the collector header of the collector; purging a gaseous fluid through a membrane into the manifold while prohibiting the passage of the liquid drug fluid through the membrane; activating an insert fit member to move the needle and cannula from the first position to a second position within a user's body; and activating a retraction fit member to move the needle from the second position to a third position, where the third position allows the passage of liquid drug fluid from the collector header of the collector through the cannula and into the user's body . In at least one embodiment of the present disclosure, the step of activating an insert fitting member to move the needle and cannula from the first position to a second position occurs after the step of purging a gaseous fluid through a membrane inside the collector. However, in an alternative embodiment, the step of activating an insertion matching member to move the needle and cannula from the first position to a second position may occur prior to the step of purging a gaseous fluid through a membrane. inside the manifold in such a way that purging through the membrane is allowed only once the needle is in the second position. Such an embodiment of a needle insertion mechanism 22200 is shown in Figures 139A-139C. In this embodiment, the fluid pressure in the fluid line can build up and force any gaseous fluid in the fluid path to the manifold to purge through the membrane, as shown in Figure 139A. Once the fluid path has been suitably pressurized in this way, the insert fit member can be fired to move the needle and cannula from the first position to a second position, thereby opening, exposing , or otherwise unblocking the membrane to evacuate the gaseous fluid from the collector. This is visible in Figure 139B. A locking or covering element 22263 such as a sleeve, cover, sleeve, or other similar component may be used outside the manifold
256 adjacent to the membrane to initially cover or block the membrane in the first position and expose or unlock the membrane in the second position to allow purging, as shown in Figure 139C. However, in any of the embodiments, the passage of the liquid drug fluid is allowed to occur only after the purge step and after the translation of the needle from the second position to the third position, where the third position allows the passage of liquid drug fluid from the collector header of the collector manifold through the cannula and into the user's body. The method may further include, prior to the step of activating a retraction adequacy member to move the needle before the second position to a third position, the step of: measuring with a sensor the substantial completion of the gas fluid purge to through the membrane.
Certain optional conventional components or variations of the insertion mechanism 21200 or drug delivery device 10 are contemplated while remaining within the scope and scope of the present disclosure. For example, the upper or lower housings may optionally contain one or more transparent or translucent windows 18, as shown in Figures 1A-1C, to allow the user to view the operation of the drug delivery device 10 or verify that the dose of drug has been completed. In addition, the drug delivery device 10 may contain an adhesive patch 26 and a patch liner 28 on the underside of housing 12. The adhesive patch 26 can be used to adhere the drug delivery device 10 to the user's body for delivery of the drug dose. As will be easily understood by the person skilled in the art, the adhesive patch 26 can have an adhesive surface for the adhesion of the drug pump to the body of the user. The adhesive surface of the adhesive patch 26 may initially be covered by a non-adhesive patch liner 28, which is removed from the adhesive patch 26 prior to the placement of the drug delivery device 10 in contact with the user's body. Adhesive patch 26 may optionally include a protective cover that prevents actuation of the optional sensor 24 on the body and covers opening 252A of the base. Removal of the patch liner 28 can remove the protective cover or the protective cover can be removed separately. Removal of the patch liner 28 can further remove the sealing membrane 254 from the insertion mechanism 21200, opening the insertion mechanism to the user's body for drug delivery.
Similarly, certain components of the present disclosure can be unified components or separate components while remaining within the scope and scope of the described embodiments. For example, the membrane is shown as a component of the collector of the insertion mechanism. The membrane may be a separate component, or it may comprise a collector wall, as will be readily understood by one of ordinary skill in the art.
257 matter. In an alternative embodiment, the membrane can be located at the distal end of the fluid line or it can be a distal part of the fluid line itself. However, the purge location allowed by the membrane determines the degree to which the system can be primed. To reduce dead volume within the fluid path and reduce gaseous fluid that can be supplied to the user, it may be desirable to have the membrane as close as possible to the end of the fluid path. Therefore, the membrane is preferably an integrated aspect of the collector of the needle insertion mechanism. Those of ordinary skill in the art will understand such conventional components and functional variations and are therefore within the scope and scope of the present disclosure.
XXII. Additional Embodiments of Fluid Path Connector
At least some of the drug delivery devices that are described in the present application, including at least those that are described in relation to Figures 1-139C, can be configured to incorporate the fluid route connector embodiments that are described in relation to Figures 140A-155. The fluid path connector embodiments described below in relation to Figures 140A-155 can be used to replace, in whole or in part, the fluid path connector 300, the fluid path connector 622, the connector Fluid path 722, Fluid path connector 922, Fluid path connector 1122, Fluid path connector 2300 described above, or any other fluid path fittings described herein, where appropriate.
In general, the present embodiments provide container connections that maintain the sterility of a fluid path and are integrated into a fluid container; drug delivery devices incorporating such sterile fluid path connectors into fluid containers; methods of operation of such devices; and methods of mounting such devices. The fluid path connectors of the present embodiments provide integrated safety features that ensure sterility of the fluid path before, during, and after fluid delivery. In one aspect, the fluid path remains disconnected from the fluid container until the device has been started by the operator. In another aspect, the fluid path maintains the sterility of a piercing member prior to connection with the fluid container within a sterile cavity prior to activation by the operator. Upon activation by the operator, at least a portion of a pierceable seal is transferred, such as by pneumatic and / or hydraulic pressure or force in the fluid, to a basically fixed piercing member such that the pierceable seal is pierced and the fluid path connects or opens to allow fluid flow through the fluid path to supply fluid from the device.
A drug delivery device, such as an infusion pump or bolus injector, may be necessary to deliver a particular amount of fluid over a period
258 of time. For example, when supplying a drug fluid subcutaneously it is important to control the fluid flow that is delivered to the patient and maintain the sterility of the fluid container and the fluid path prior to activation or operation of the fluid delivery device. . It may be desired that the fluid path connector remain disconnected, for container integrity, sterility, or other purposes, until the user has activated the device and started fluid flow from a container. Some drug delivery devices may use one or more active fluid path control mechanisms to prevent a premature fluid path or drug delivery connector. Other drug delivery devices are configured in such a way that the fluid path connector is made after fabrication, and the fluid delivery is blocked until desired by the user. Such designs do not provide the beneficial advantages associated with maintaining the integrity of the container and sterility of the internal components of the drug delivery device. The present embodiments provide an integrated fluid path connector mechanism for sterile drug delivery devices. These new embodiments both provide a connection mechanism to open or connect a sterile fluid path between a fluid container and a fluid passage, without adding unnecessary steps to the user. This is allowed by activation of the action and translation mechanism of the plunger seal, resulting in pneumatic and / or hydraulic pressure within the fluid that forces the translation of at least part of a pierceable seal, causing it to impact on a piercing member basically stationary, thereby opening a sterile fluid path between the fluid container and the fluid passage.
Therefore, embodiments of the present disclosure provide a sterile fluid path connector that is integrated into a fluid container and is opened, connected, activated, or otherwise enabled by operation of the device and mechanism of action. Activation of the action mechanism and the force transferred from the action mechanism to the plunger seal is itself used to open a sterile fluid path between the fluid container and the fluid passage. Therefore, the integrity and sterility of the fluid container can be maintained prior to and during operation of the device. This new configuration also automates the stage of the sterile fluid path connector, greatly reducing the complexity of the device and the necessary operational steps that are performed by the device or the user. New embodiments of the present disclosure also allow flexibility in device component configurations, and reduce overall device footprint or distribution because no separate sterile fluid path connector mechanism is required on the cap side of the container. of fluid. The present embodiment can also be fully implemented or used in conventional sterile fluid production, including drug filling completion processes,
259 including applications that require vacuum extraction. Furthermore, the present embodiments can also integrate a variety of different status indication mechanisms into the device, including using the piercing member or the plunger seal as parts of an indication mechanism that indicates the status of fluid transfer from the fluid container. sterile fluid to the connector. For example, when the fluid container is a drug container, such components and devices provide an end-of-dose indication coupled to the actual travel and drug delivery status of the plunger seal.
At least one embodiment provides a sterile fluid path connector that includes a piercing member, a connector shaft, and a pierceable seal. More specifically, at least one embodiment provides a sterile fluid connector comprising a first part configured to connect a sterile fluid path and a second part comprising a housing configured to mount a sterile fluid container; a connector shaft; a pierceable seal disposed at least partially between the connector shaft and the sterile fluid container and forming a sterile fluid chamber between the connector shaft and the pierceable seal; and a piercing member disposed within the connector shaft capable of providing sterile fluid communication between the sterile fluid chamber and the sterile fluid path; where at least a portion of the pierceable seal is configured to transform from an unactivated state in which the pierceable seal is intact, to an activated state in which the pierceable seal is altered by the piercing member to create sterile fluid communication between the sterile fluid container and the sterile fluid path. The housing can also be configured to hide a part of the connector inside the sterile fluid container. The connector shaft may further comprise at least one port or discharge. The sterile fluid path may also include at least one sensor configured to indicate the status of fluid transfer from the sterile fluid container to the connector. Additionally, the sterile fluid path connector can include one or more flow restrictors. In at least one embodiment, the connector shaft can function at least partially as a fluid line or a flow restrictor. In at least one embodiment, the fluid path connector further includes a filter. A variety of known filters can be used in the embodiments of the present disclosure, which will be readily understood by one of ordinary skill in the art. For example, the filter may comprise a permeable membrane, a semi-permeable membrane, or a porous membrane, which encloses the sterile cavity of the external environment.
The piercing member is initially retained in a basically fixed position within the sterile cavity between the connector shaft and the pierceable seal. Upon activation by the operator (eg, a patient), at least a portion of the pierceable seal is caused to move to a second position where the piercing member penetrates the pierceable seal. The force, such as a pneumatic and / or hydraulic force, applied to the pierceable seal on the
260 opposite side to the sterile cavity, causes the translation of at least a part of the pierceable seal towards the piercing member. The translation of the pierceable seal causes it to impact the basically stationary or fixed piercer member to open a fluid path through the pierceable seal. Therefore, at least a portion of the pierceable seal is configured to move from the first position to the second position by the force applied by a fluid on the pierceable seal. Penetration of the pierceable seal by the piercing member after movement of a portion of the pierceable seal from the first position to the second position opens a fluid path through the pierceable seal and the piercing member into a fluid conduit.
In at least one embodiment, the pierceable seal comprises a seal barrier that can be penetrated by the piercing member. The piercing member may initially be in contact with, or adjacent to, the seal barrier.
The fluid path connector may further include a piercing member guide, where the piercing member guide is capable of engaging or traveling on the connector shaft. The piercing member guide may function to ensure that the pierceable seal, or at least a portion thereof such as a seal barrier, properly contacts and travels with the piercing member to pierce and open the fluid path. through the pierceable seal and piercing member to a fluid conduit.
The piercing member can be configured to pass the connector shaft and connect to a fluid line. In another embodiment, the connector shaft can connect the piercing member to the fluid conduit, and the fluid conduit can be at least partially a part of the connector shaft. In at least one embodiment, the fluid passage passes to the connector shaft at a port on the connector shaft.
In at least one embodiment, the sterile fluid connector includes at least one sensor configured to indicate the state of fluid transfer from the sterile fluid container to the connector. For example, the sterile fluid path connector may further include one or more interconnects, and optionally one or more corresponding contacts, to transmit a signal to the user. For example, the interconnect (s) may be within or at least partially proximal to a transferable piston seal in a fluid container such that the piercing member is capable of penetrating the piston seal and acting as a contact or contacts. for interconnection or interconnections to transmit a signal to the user. In addition, or alternatively, the interconnect (s) or the contact (s) are within or at least partially proximal to a transferable plunger seal within a drug container and the other is within or at least partially distal to the pierceable seal to transmit a signal to the user when the plunger seal and pierceable seal are basically in contact. In addition, or alternatively, the interconnection or
261 Interconnects and the contact (s) are within a sterile cavity between the connector shaft and the pierceable seal in such a way that releasing pneumatic and / or hydraulic pressure at the end of fluid transfer releases the interconnect to transmit or cease the transmission of a signal to the user. A variety of known interconnections and contacts can be used in the embodiments of the present disclosure, which will be readily understood by one of ordinary skill in the art. For example, a variety of: Hall effect sensors; magnetic field sensors or giant magnetoresistance (GMR); optical sensors; capacitive or capacitance change sensors; ultrasonic sensors; and linear travel sensors, LVDT, linear resistive, or radiometric linear resistive; and combinations thereof, which are capable of coordinating to transmit a signal to the user.
Another embodiment provides an integrated fluid path connector and a drug container having a piercing member, a connector shaft, and a pierceable seal integrated at least partially within a drug container having a barrel and a plunger seal. The pierceable seal is transferable to a basically stationary piercing member, and the pierceable seal is configured to move from a first position, where the piercing member is located within a sterile cavity between the connector shaft and the pierceable seal, to a second position , where the pierceable seal has been penetrated by the piercing member. The fluid container contains a fluid chamber between the pierceable seal and the plunger seal to initially retain fluid, and the pierceable seal is configured to move from the first position to the second position by a force applied by the fluid on the seal perforable. In at least one embodiment, the pierceable seal has a seal barrier that can be penetrated by the piercing member, and the piercing member is initially in contact with, or adjacent to, the seal barrier.
The integrated fluid path connector may further include a piercing member guide piece attached to the piercing member or connector shaft, where the piercing member guide slidably engages the connector shaft or piercing member to allow translation of the pierceable seal, or a portion thereof, in the direction of fluid outlet from the connector. Translation of the pierceable seal in the direction of the fluid container can be prevented by retaining a portion of the pierceable seal by, for example, a housing, such as a crimped plug, mounted to the fluid container barrel that retains the connector shaft , the piercing member, and the pierceable seal in place during operation. The configuration can be used to allow the fluid chamber of the fluid container to be evacuated, such as by vacuum, before filling with a fluid without compromising the function of the sterile fluid path connector.
In at least one embodiment, the connector shaft has a header with a port for
262 conduit, a chamber, and a vacuum port with a channel leading to the chamber such that the sterile cavity can be evacuated through the channel. The conduit port may have a membrane or seal that allows fluid flow out of the chamber, and may be capable of being plugged. Similarly, the vacuum port may be capable of being plugged, such as by a polymeric plug. Such configurations allow, for example, the sterile cavity to be evacuated to maintain both sterility and pressure balance between the sterile cavity and the opposite side of the pierceable seal, or otherwise assist in maintaining the relative positions of the components prior to or during the operation of the device by the user.
In at least one embodiment, the pierceable seal, or at least a portion thereof, is transferable to the piercing member and the pierceable seal is further configured to move from the second position, where the pierceable seal has been penetrated by the piercing member, to a third position where at least one sensor indicates the state of fluid transfer from the sterile fluid container to the connector. For example, in a third position, one or more interconnects and one or more corresponding contacts are allowed to transmit a signal to the user. In one such embodiment, the interconnect (s) or the contact (s) is in one aspect of an actuation mechanism and the other is within or at least partially proximal to the piston seal to transmit a signal to the user when the piston seal and the pierceable seal are basically in contact. Alternatively, the interconnect or interconnects or the contact or contacts is within or at least partially distal to the pierceable seal and the other is proximal to the connector shaft to transmit a signal to the user when the plunger seal and the pierceable seal are basically in contact. In addition, or alternatively, the interconnect with interconnects and the contact or contacts are within a sterile cavity between the connector shaft and the pierceable seal in such a way that the release of pneumatic and / or hydraulic pressure at the end of the dose releases the interconnection to transmit or cease the transmission of a signal to the user. A variety of known interconnections and contacts can be used with the present embodiments, which will be readily understood by one of ordinary skill in the art. For example, a variety of: Hall effect sensors; magnetic field sensors or giant magnetoresistance (GMR); optical sensors; capacitive or capacitance change sensors; ultrasonic sensors; and linear travel sensors, LVDT, linear resistive, or radiometric linear resistive; and combinations thereof, which are capable of coordinating to transmit a signal to the user.
Yet another embodiment provides a drug delivery device with integrated sterility maintenance features comprising a housing within which an activation mechanism, an insertion mechanism, and a fluid container having a plunger seal can be mounted. The fluid container is connected in a
263 end to an action mechanism and at the other end to a fluid path connector. The fluid path connector includes a piercing member, a connector shaft, and a pierceable seal, where the piercing member is retained within a sterile cavity between the connector shaft and the pierceable seal, and where the pierceable seal is configured to moving from a first position to a second position where the pierceable seal has been penetrated by the piercing member. The fluid container contains a fluid chamber between the pierceable seal and the plunger seal to initially retain fluid, and where the pierceable fluid seal is configured to move from the first position to the second position by a force applied by the fluid on the pierceable seal. In at least one embodiment, the pierceable seal has a seal barrier that can be penetrated by the piercing member, and the piercing member is initially in contact with, or adjacent to, the seal barrier.
The drug delivery device may further include a piercing member guide coupled to the connector shaft or piercing member, wherein the piercing member guide slidably couples the connector shaft or piercing member to allow translation of the pierceable seal, or a part of it, in the distal direction (that is, towards the fluid conduit from where the fluid leaves the connector). Translation of the pierceable seal in the proximal direction can be prevented by retention of the pierceable seal, or a portion thereof by, for example, a housing such as a barrel-mounted crimped plug, housing retaining the connector shaft, the piercing member , and the pierceable seal in place during operation. Such a configuration can be used to allow the drug chamber of the drug container to be evacuated, such as by vacuum, prior to filling with a fluid without compromising the function of the sterile fluid path connector. In at least one embodiment, the connector shaft has a header with a conduit port, a chamber, and a vacuum port with a channel leading to the chamber such that the sterile cavity can be evacuated through the channel. . The conduit port may have a filter, membrane, or seal to allow or restrict fluid flow out of the chamber. Similarly, the vacuum port may be capable of being plugged, such as with a polymeric plug. Such configurations may, for example, allow the sterile cavity to be evacuated to maintain sterility, maintain the pressure balance between the sterile cavity and the opposite side of the pierceable seal, or assist in maintaining the relative positions of the components before or during the operation of the device by a user.
In at least one embodiment, the pierceable seal is movable on the piercing member or an aspect of the connector shaft and is further configured to move from the second position, where the pierceable seal has been penetrated by the piercing member, to a third position where One or more interconnects and one or more corresponding contacts are allowed to transmit a signal to the user. The interconnection (s) and the
264 Corresponding contact or contacts are configured such that, for example: (a) the interconnect to interconnects or the contact or contacts is located on one aspect of the mechanism of action and the other is located within or at least partially proximal to the seal plunger, to transmit a signal to the user when the plunger seal and the pierceable seal are basically in contact; (b) the interconnect or interconnects or the contact or contacts is located within or at least partially distal to the pierceable seal and the other is located proximal to the connector shaft, to transmit a signal to the user when the plunger seal and the pierceable seal they are basically in contact; (c) The interconnect (s) and the contact (s) are located within the sterile cavity between the connector shaft and the pierceable seal, such that after the seal is punctured, continued pressure within the drug chamber causes a interconnection that transmits a signal to the user, a signal that ends once the pressure inside the drug chamber drops and the interconnection is lost, that is, at the end of the dose. A variety of known interconnections and contacts can be used with the present embodiments, which will be readily understood by one of ordinary skill in the art. For example, a variety of: Hall effect sensors; magnetic field sensors or giant magnetoresistance (GMR); optical sensors; capacitive or capacitance change sensors; ultrasonic sensors; and linear travel sensors, LVDT, linear resistive, or radiometric linear resistive; and combinations thereof, which are capable of coordinating to transmit a signal to the user.
Additionally, fluid path connectors can include one or more flow restrictors. In at least one embodiment, the connector shaft can function at least partially as a fluid line or a flow restrictor. In at least one embodiment, the fluid path connector further includes a filter. A variety of known filters can be used with the embodiments of the present disclosure, which should be readily understood by one of ordinary skill in the art. For example, the filter may be a permeable membrane, a semi-permeable membrane, or a porous membrane, which encloses the sterile cavity of the outer medium.
The new devices of the present embodiments provide container fluid path connectors that maintain fluid path sterility and that are integrated into the fluid container, and drug delivery devices that incorporate such integrated sterile fluid path connectors. to fluid containers. Because the fluid path is disconnected until fluid supply is desired by the operator, the sterility of the fluid path connector, the fluid container, the fluid, and the entire interior of the device are maintained. Furthermore, the new configurations of fluid path connectors and drug delivery devices of the present disclosure maintain sterility of the fluid path through operation of the device. Because the path the fluid travels within the device is kept completely sterile,
265 These components need only be sterilized during the manufacturing process. Such components include the fluid container of the action mechanism, the fluid path connector, the sterile fluid passage, and the insertion mechanism. In at least one embodiment of the present disclosure, the power and control system, mounting platform, control arm, trigger mechanism, housing, and other components of the drug delivery device do not need to be sterilized. This greatly improves the manufacturing capacity of the device and reduces associated mounting costs. Therefore, the devices of the present embodiments do not require terminal sterilization upon completion of assembly. A further benefit of the present embodiments is that the components described herein are designed to be modular in such a way that, for example, the fluid path connector and other components of the device can be integrated into a housing and connect to function as a drug delivery device.
A further embodiment provides a method of mounting an integrated sterile fluid path connector and fluid container. The sterile fluid path connector can be first mounted and then joined, mounted, connected, or otherwise integrated into the fluid container such that at least a portion of the pierceable seal is contained within the drug container. The fluid container can then be filled with fluid for user supply and capped with a plunger seal at an opposite end of the pierceable seal. The barrel can be filled with fluid through the open proximal end prior to insertion of the plunger seal from the proximal end of the barrel. An action mechanism can also be attached to the proximal end of the fluid container in such a way that a component of the action mechanism is able to contact the plunger seal. An insertion mechanism can be mounted and attached to the other end of the fluid line. This complete subassembly, which includes an action mechanism, drug container, fluid path connector, fluid line, and insertion mechanism, can be sterilized, as described above, prior to mounting in a drug delivery device. Certain components of this subassembly can be mounted on a mounting platform inside the housing or directly inside the housing, and the other components can be mounted to a guide, channel, or other component or aspect for user activation. One method of manufacturing a drug delivery device includes the step of attaching both the fluid path connector and the fluid container, either separately or in the form of a combined component, to a device mounting platform or housing. drug delivery. The manufacturing method further includes attaching the action mechanism, the fluid container, and the insertion mechanism to the mounting platform or housing. Additional components of the drug delivery device, as described in
266 This document, which includes the power and control system, the trigger mechanism, and the control arm, can be attached, pre-formed, or pre-assembled to the mounting platform or housing. In the case where the fluid is a drug, and the drug delivery device is an ambulatory infusion device, an adhesive patch and a patch liner can be attached to the surface of the drug delivery device housing that Contact the user during the operation of the device.
A method of operating the drug delivery device includes one or more of the following steps: activating the activation mechanism by the user; move a control arm to operate an insertion mechanism; activate an action control mechanism to push the plunger seal, connect the sterile fluid path connector, and direct fluid flow through the drug delivery device; where the pressure of the plunger seal transfers the fluid and thereby causes the pierceable seal to deform in the direction of the fluid passage and be pierced by a piercing member, thereby opening a fluid path from the fluid container to the fluid line. The action control mechanism can be activated by operating a power and control system. The method may further include the step of: attaching a sensor to the optional body prior to activating the trigger mechanism. In addition, the method of operation may include moving a plunger seal into the action control mechanism and the fluid container to force fluid flow through the fluid container, the fluid path connector, the fluid line, and the insertion mechanism for supplying the fluid to the desired target, for example, to the body of a patient.
The new devices of the present embodiments provide container connections that maintain fluid path sterility and that are integrated into the fluid container, and drug delivery devices that incorporate such sterile fluid path connectors integrated into the fluid containers. fluid. For example, such devices are safe and easy to use, and are aesthetically and economically attractive to self-administered patients.
In at least one embodiment, the sterile fluid path connector disclosed herein includes a piercing member, a connector shaft, and a pierceable seal; where at least a portion of the pierceable seal is configured to move from a first position where the piercing member is retained within a sterile cavity between the pierceable seal and the connector shaft, to a second position where the pierceable seal has been penetrated by the piercing member. A filter can be used to enclose the sterile cavity of the external medium. Such fluid path connectors can be integrated into a fluid container having a barrel and a plunger seal. The components of the fluid path connector may further be capable of transmitting a signal to the user upon completion of the fluid supply, for example, upon contact between the plunger seal and the pierceable seal.
267
A fluid supply pump includes such fluid path connectors and integrated fluid containers.
The new embodiments presented herein provide sterile fluid path connectors and integrated drug containers, and drug delivery devices utilizing such connections, configured to maintain sterility of the fluid path before, during, and after of device operation, and that enable active security controls for the device. Integration of the fluid path connector into a part of the fluid container helps to ensure the integrity and sterility of the fluid path container. In addition, by integrating the sterile fluid path connector into a part of the fluid container, the fluid transfer connection can be controlled by the user (i.e., user activated) and enabled by the function of the action mechanism . Therefore, the user activation steps and the internal operation of the drug delivery device can be greatly simplified by the new integrated sterile fluid path connectors of the present embodiments.
The new embodiments provide container connections that maintain fluid path sterility and are integrated into the fluid container, and drug delivery devices that incorporate such integrated sterile fluid path connectors into fluid containers. The present embodiments also further integrate the sterile route connector into the fluid container, to reduce the required components or to provide easier and more efficient operation of the drug connection and delivery devices. The connector, sterile fluid path assembly, and infusion pump disclosed herein are not limited to medical applications, but include any application, including industrial uses, where the supply of sterile fluid may be desired or uncontaminated. When the fluid is a drug, the present embodiments provide devices that are safe and easy to use, and are aesthetically and ergonomically attractive to self-administered patients. The embodiment described herein incorporates features that make activation, operation, and closure of the device simple even for untrained users. One or more components of the present embodiments may be modular in that, for example, they may be preassembled in the form of separate components and configured in position within the housing of the drug delivery device during manufacture.
Figure 140A and Figure 140B show an initial configuration of one embodiment of a sterile fluid path connector 23030 integrated with a fluid container 23050 having a fluid chamber 23021 and a plunger seal 23060. In some embodiments, the fluid path connector 23030 and fluid container 23050 can be partially or fully replaced by the fluid path connector 30 and fluid container 50 illustrated in the
268
Figure 1B of the present application. Fluid path connector 23030 can be permanently attached, removable, connected, or otherwise attached to a fluid container 23050 at an opposite end of plunger seal 23060. As shown in the embodiment of Figure 140A and Figure 140B, fluid container 23050 has a mutable fluid chamber 23021 with a barrel 23058, defined by the position of pierceable seal 23056 and plunger seal 23060. The seals described herein can be made from a variety of materials, but are generally made from one or more elastomers or rubbers. Fluid chamber 23021 may contain a fluid for delivery through the integrated sterile fluid path connector 23030. In the embodiment of Figure 140A and Figure 140B, the fluid path connector 23030 includes the sterile fluid line 23035, the piercing member 23033, the connector shaft 23031, and the pierceable seal 23056. The path path connection 23030 Fluid includes piercing member guide 37 coupled to connector shaft 23031, after which pierceable seal 23056 may connect to piercing member 23033 or connector shaft 23031 during operation. A permeable, semi-permeable, or porous membrane, such as filter 23039, can be used to allow air discharge from within the fluid path connector 23030 during device operation, such as through port or discharge 23031B in the connector shaft 23031. Filter 23039 can be attached, mounted, set, overmolded, co-molded, preformed, or otherwise connected to enclose sterile cavity 23032 between the exterior of connector shaft 23031 and pierceable seal 23056. The term enclosure or enclosure is used herein to define at least one semipermeable or porous confined area that can be sterilized, evacuated by vacuum, and discharged, but is not penetrable by microorganisms, contaminants, or other unwanted environmental factors. For example, filter 23039 can be at least partially overmoulded with connector shaft 23031 to separate sterile cavity 23032 from the external medium. In some embodiments, the filter is a membrane, eg, a semi-permeable membrane, that allows air discharge during actuation of pierceable seal 23056, fluid path connection 23030, and pump device. Filter 23039 can be sterilized by methods well known to those of ordinary skill in the art, and thus the filter can maintain a sterile barrier to prevent exposure of piercing member 23033 to microorganisms, contaminants, or other undesirable environmental factors.
As shown in Figure 140B, piercing member 23033 is retained within integrated sterile fluid path connection 23030, at or near piercing seal seal barrier 23056C 23056. Piercing member 23033 may be an aspect of the conduit 23035 fluid or it can be a separate component of fluid conduit 23035, as will be easily understood by the person skilled in the art. In addition, the route 23030 connector
269 Fluid may optionally include one or more gaskets, O-rings, or other sealing members, compressed for sealing between barrel 23058, particularly at edge 23058A, connector shaft 23031, and casing 23052. In at least one embodiment , the sealing aspect 23056A of the pierceable seal 23056 can be configured as a seal between the barrel edge 23058A, the connector shaft 23031, and the casing 23052. Housing 23052 may be a separate component, such as a crimp plug, or may be an aspect of connector shaft 23031 capable of mounting to barrel 23058. The housing or plug also has threads configured to complement the threads of a fluid container , or use other non-permanent means to connect the fluid container to the sterile fluid path connector. As shown in Figure 140A and Figure 140B, the sterile fluid path connector 23030 can be attached to (ie, integrated with) fluid container 23050; which in turn can be mounted, by a variety of known methods, either fixedly or removably to a mounting platform or casing of a fluid pump, such as drug delivery device 10 as shown in the Figures 1A-1C. The mounting platform may be a separate component of the housing, or it may be a unified component of the housing such as a preformed mounting appearance on the interior surfaces of the housing. In such configurations, the sterility of the fluid path is maintained, the path for fluid flow is not connected until desired by the user, and user-initiated activation causes the fluid chamber to connect and the fluid path. The fluid path connection may further optionally include one or more flow restrictors or one or more of a piercing member 23033 and a flow conduit 23035 may further function as flow restrictors.
The integrated fluid connection of the present embodiments is further illustrated by reference to a mechanism of action, shown in Figure 141A and Figure 141B. The embodiment comprises a fluid conduit 23035, coupled with piercing member 23033 in coupling 23038, a connector shaft 23031 including discharge 23031B, filter 23039 being housed against connector shaft 23031, pierceable seal 23056, the portion of which Seal 23056A adjoins connector shaft 23031 and barrel end 23058, all of which is housed in plug 23052. Barrel 23058 comprises mutable fluid chamber 23021, and houses piston seal 23060 which is slidably disposed therein and in contact with an action mechanism (eg, the action mechanism 50 illustrated in Figure 1B), which includes an adequacy member 23099. Figure 141A is an exploded side view of the components of an integrated sterile fluid path connector and fluid container according to at least one embodiment. Figure 141B shows an exploded sectional view of the same embodiment. Sterile fluid path connector 23030 can be integrated at least partially into fluid container 23050 at an opposite end of plunger seal 23060. An exemplary 23090 mechanism of action is shown in
270 these figures to clarify the orientation of these components. The components of the new 23030 sterile fluid path connection can be preassembled (see, for example, Figure 143A) and then permanently, removably attached, mounted, connected, or otherwise paired with a fluid container such as fluid container 23050.
A variety of mechanisms of action can be used to force fluid from a fluid container for delivery. In one such embodiment, mechanism of action 23090 may be basically similar to that described in WO 2013/023033467 (PCT / US2012 / 023052303241). The components of the mechanism of action upon activation can be used to drive axial translation in the distal direction (i.e., toward housing 23052 of Figure 140) of the fluid container plunger seal. Optionally, the mechanism of action may include one or more compliance features that allow for additional axial translation of the plunger seal to ensure, for example, that the full drug dose has basically been delivered to the user and that the feedback contact mechanisms have been connected or interconnected. Furthermore, the mechanism of action may include one or more security mechanisms, such as premature activation prevention mechanisms, to enhance the security and usability of the mechanism and the device.
In a particular embodiment, the action mechanism 23090 employs one or more compression springs 23099 as the matching member or members, as shown in Figure 141B. After activation of the fluid pump by the user, the power and control system is actuated to directly or indirectly release the compression spring or springs from an energized state. After release, the compression spring or springs can press and act on the plunger seal 23060 to force the fluid out of the mutable fluid chamber 23021 of the drug container 23050 as further described by reference to Figures 142A-142C. .
Figure 142Aa to Figure 142C illustrate the features of an embodiment before use, after piercing the pierceable seal, and after completion of fluid delivery. More specifically, in the configuration shown in Figure 142A, piercing member 23033 is maintained within sterile cavity 23032 with a first end (a proximal end) adjacent to, or in contact with, pierceable seal 23056 of connector 23030. fluid path. The sterility of cavity 23032 and piercing member 23033 is maintained, for example, by filter 23039 disposed between sterile cavity 23032 and the outer medium. In at least one embodiment, as shown in Figure 142, filter 23039 is connected to, coupled with, or part of connector shaft 23031, and encloses sterile cavity 23032 in the outer medium. Sterile cavity 23032 can be discharged through the discharge or port 23031B within the shaft connection 23031. Therefore, the fluid path connector 23030,
271 in at least one embodiment, it is mounted on and integrated with fluid container 23050, for example by housing (stopper) 23052 coupled with rim 23058A of barrel 23058. The piercing member may be a variety of cannulas or conduits, such as rigid needles , and can be comprised of a variety of materials, such as steel. In at least one embodiment, piercing member 23033 is a rigid steel needle. The pierceable seal 23056 may have a sealing appearance 23056A that allows the pierceable seal 23056 to be mounted directly to or otherwise held in place between the barrel 23058, the connector shaft 23031, and the plug 23052. The connector shaft 23031 Includes an internal seal mount 23034 that further stabilizes the position of more stationary aspects of the pierceable 23056 membrane. At least a portion of the pierceable seal 23056, such as seal barrier 23056C, can be translated over connector shaft 23031, as described herein, to break in front of piercer member 23033 and allow fluid path connection to conduit 23035 of sterile fluid. Advantageously, such an arrangement allows pierceable seal 23056 to translate into plug 23052 but not into piston seal 23060. This is a desirable feature that allows the mutable fluid chamber 23021 of the fluid container 23050 to be evacuated, such as by vacuum, prior to filling with a fluid without compromising the function of the sterile fluid path connector 23030.
In an initial position the proximal end of piercing member 23033 may reside adjacent to, or in contact with, seal barrier 23056C of pierceable seal 23056, for example, to minimize the travel distance of seal barrier 23056C to be pierced. and open fluid container 23050 to fluid path connector 23030. In a particular embodiment, the proximal end of piercing member 23033 may reside at least partially within seal barrier 23056C of pierceable seal 23056, although not yet fully passing therethrough, until user activation of the device.
As shown in Figure 142B, once the pump device is activated and the action mechanism pushes the plunger seal 23060, the plunger seal 23060 exerts a force on fluid chamber 23021, and pneumatic pressure is produced and / or hydraulic by compression of the fluid in chamber 23021. When pneumatic and / or hydraulic pressure occurs within fluid chamber 23021, the force is transmitted to pierceable seal 23056, causing barrier seal 23056C to transform. That transformation may include a displacement, inversion, translation, flexion, deformation, jump, click, or any other functionally equivalent change, such that a part of the perforable seal 23056, such as the seal barrier 23056C, impinges against the basically fixed position of piercing member 23033 and causing piercing member 23033 to pierce pierceable seal 23056 into seal barrier 23056C, as shown in Figure 142B, thereby opening or
272 otherwise connecting the fluid path between mutable fluid chamber 23021, piercing member 23033, and fluid conduit 23035.
Therefore, the integrated sterile fluid path connector 23030 is connected (i.e., the fluid path is opened) by the pneumatic and / or hydraulic force of the fluid within the fluid chamber 23021 created by activation of the action mechanism. . Once the integrated sterile fluid path connection 23030 is connected or opened, fluid is allowed to flow from the fluid container 23050, through the integrated sterile fluid path connection 23030 and the sterile fluid conduit 23035. In aspects where the fluid pump is an ambulatory drug infusion pump, the fluid drug then flows through the insertion mechanism and into the user's body for drug delivery. In at least one embodiment, a variety of flow restrictors can optionally be used to modify fluid flow at the fluid path connection. In at least one embodiment, fluid flows only through a manifold and an insertion mechanism cannula or needle, thereby maintaining sterility of the fluid path before and during fluid delivery.
In addition, or alternatively, the plunger seal 23060 or the pierceable seal 23056 may have some compressibility allowing a fluid compliance push from the drug container 23050. In addition, the actuation mechanism, plunger seal 23060, connector shaft 23031, pierceable seal 23056, or a combination thereof, may include one or more sensors or status indication mechanisms, such as interconnects and contacts, to measure and report the status of the drug delivery action before, during, and after operation of the fluid delivery device.
Figure 142C shows the components of the fluid container 23050 and the connector
23030 sterile fluid path after basically all fluid has been expelled from fluid container 23050. In particular, the plunger seal 23060 is in the most distal position on barrel 23058. In the embodiment of Figure 142C, the shaft side connector (eg, distal end) of plunger seal 23060 is configured with an optional protrusion and cavity appearance 23069, structure that minimizes residual volume remaining in the chamber 23021 fluid, now collapsed. Alternatively, the plunger seal may be a flat-faced plunger seal (for example, plunger seal 23160 of Figure 144A and Figure 145), or it may have any number of other configurations as will be readily understood by one of ordinary skill in the art. The matter. In the embodiment shown in Figure 142, plunger seal 23060 further comprises interface / contact 23061; and connector shaft 23031 further comprises interface / contact 62. At the end of supply, the interconnection / contact 61 of the piston seal 23060 and the interconnection / contact 62 of the shaft
23031 of connector interconnect and transduce a signal that can be perceived by the user. As described herein, numerous sensors can be incorporated and
273 signal transduction means or adapted for use in the present embodiments.
Due to the new design of the fluid path connector of the present embodiments and its integration at least partially into the fluid containers, the sterility of the fluid path is maintained in the transportation, storage, and operation of the device; user activation of the device is simplified; and the fluid path is only connected when desired by the user. The sterility of the fluid path connection is initially maintained to carry out the connection within a sterile cavity 23032 between the connector shaft 23031, the pierceable seal 23056, and the piercer member guide 23037. In at least one embodiment, the sterility of cavity 23032 is maintained by filter 23039 which is adjacent to, coupled to, or is part of, connector shaft 23031. Filter 23032 may be, for example, a semipermeable membrane that allows air discharge through discharge 23031B of connector shaft 23031 during actuation and translation of pierceable seal 23056. Filter 23039 can be sterilized by standard sterilization methods, which will be readily understood by one skilled in the art, and can be used to maintain a sterile barrier that prevents exposure of piercing member 23033 to microorganisms, contaminants, or other unwanted environmental factors. . For example, upon basically simultaneous activation of the insertion mechanism, the fluid path between mutable fluid chamber 23021 and the insertion mechanism is completed to allow delivery of drug to the user's body. Because fluid path connector 23030 is not in fluid connection or communication with fluid chamber 23021 until activation of the fluid pump and actuation mechanism, fluid flow from fluid container 23050 is prevented until desired by the user. This provides an important safety feature to the user and also maintains the container integrity of the fluid container and the sterility of the fluid path.
The action mechanism that carries the plunger seal 23060 may contain one or more action matching members (eg, as shown in Figure 141B). The components of the action mechanism operate to force a fluid from the mutable fluid chamber 23021 through pierceable seal 23056 and through piercing member 23033 or sterile fluid passageway 23035, for delivery through fluid path connector 23030. . Furthermore, regarding the mechanism of action, a variety of mechanisms of action can be used to force fluid from a drug container for delivery to a user's body. In one such embodiment, mechanism 23090 of action may be basically similar to that described in WO 2013/023033467 (PCT / US2012 / 023052303241), which is hereby incorporated by reference in its entirety. The components of the mechanism of action, upon activation, lead to axial translation in the distal direction of the plunger seal of the drug container. Finally, the mechanism of action may include one or more compliance features that allow axial translation.
274 in addition to the plunger seal, for example, to ensure that the full fluid dose has basically been delivered to the user and to ensure that the feedback contact mechanisms have been connected. Furthermore, the mechanism of action may include one or more security mechanisms, such as premature activation prevention mechanisms, to enhance the security and usability of the mechanism and the device.
At least one embodiment provides a modular fluid path connection. Figure 143A and Figure 143B detail an embodiment of a modular fluid path connector comprising a connector shaft 23031, which is adjacent to filter 23039 and pierceable seal 23056 in sealing member 23056A. Connector shaft 23031, filter 23039, and pierceable seal 23056 are housed within plug 23052, as shown in Figure 143A. Connector shaft 23031 further comprises header 23031C, which forms a junction for fluid line 23035 and piercing member 23033. As shown in Figure 143A and Figure 143B, fluid line 23035 can be connected directly to the member perforator 23033. Alternatively, as shown in Figure 144A, fluid line 223035 can be connected through line port 223038. However, a modular fluid path connection can be adapted for use with a variety of alternative barrel and action configurations, and used in a variety of ambulatory infusion devices. The components of the new sterile fluid path connector 23030 can be pre-assembled, to appear as shown by way of example in Figure 143A, and basically attach, mount, connect, or otherwise pair with a fluid container such as fluid container 23050. Alternatively, the components of the sterile fluid path connector 23030 can be mounted directly to the drug container 23050. As will be readily understood by the person skilled in the art, a variety of glues or adhesives, or other connection methods such as quick release installation, interference installation, screw installation, fusion joint, soldering, ultrasonic welding, soldering, can be used. with laser, and mechanical fixation, and the like, to couple one or more of the components described herein in permanent or non-permanent connection as desired for a particular use. For example, glue can be used between the distal end of barrel 23058, the sealing member 23056A, or the connector shaft 23031A. In addition, or alternatively, the components of the sterile fluid path connector 23030 can be mounted to the barrel 23058 and hold in place a crimped plug 23052 in the distal aspect of the barrel 23058, such as a flanged appearance or edge of the barrel 23058A.
In at least one embodiment, as shown in Figure 144A to Figure 144C, piercing member guide 230237 can be used to guide pierceable seal 23056 and slidably engage connector shaft 230231. In addition, or alternatively, piercing member guide 230237 can be used to ensure that the piercing member
275
230233 basically remain centered on the shaft so that it pierces the pierceable seal 23056 in the desired part of the seal barrier 23056 C. The embodiment of Figure 144A shows a fluid container comprising a barrel 23058 and forming a fluid chamber 23021 changeable between the plunger seal 230260 and the pierceable seal 56. As shown in Figure 144A, plunger seal 230260 is a flat plunger seal, but a variety of forms of plunger seal can be adapted for use with the fluid connection and infusion pumps of the present embodiments. The embodiment of Figure 144A further comprises filter 23039, which is adjacent to connector shaft 230231 and is used to maintain the sterility of sterile chamber 23032 between connector shaft 230231 and pierceable seal 23056. Connector shaft 230231 also includes a seal mount 230234 that is adjacent to pierceable seal 23056; and a flange 230231A which is abutting with the seal seal member 23056A 23056 and which, in turn, is abutting the distal edge 23058A of the barrel 23058. The surfaces found of the connector shaft 230231A, the sealing member 23056A and the Barrel edge 23058A snaps into place and secures within the edges of plug 23052. Connector shaft 230231 also has a vacuum port 230231B, a filtered channel leading to sterile chamber 230232. Connector shaft 230231 is also configured with conduit port 230231D, which provides the outlet of connector 230230 for sterile fluid to the remainder of the infusion device (eg, injection means), such as through a sterile fluid line 230235 (not shown). The conduit port 230231D and the vacuum port 230231B may contain a membrane or seals, such as one-way seals, that allow fluid to flow out of chamber 23032 through the respective ports but does not allow fluid to flow into camera 23032 through these ports. In addition, or alternatively, the conduit port 230231 D and the vacuum port 230231B may be plugged at certain points of mounting or operation. For example, vacuum port 230231 B can be used to evacuate sterile cavity 23032 during fabrication, assembly, or at any point prior to device operation; and then vacuum port 230231B can be plugged after evacuation is complete.
For additional reference to piercing member guide 230237, this component can be slidably attached to connector shaft 230231. A variety of means known in the art can be used to facilitate this sliding connection such as, for example, coupling between the connector tip 230237D and the leg 230237A of the piercing member guide 230237 with the complementary cavity 230236 in the shaft 230231 of connector. These components are more clearly visible in Figure 144A and Figure 144B. Figure 144B shows the orientation of piercing member 230233 in piercing member guide 230237, emerging from piercing member guide 230237 in header 230237C; and Figure 144C shows the orientation of piercing member 23033 and guide 230237 of
276 piercing member within connector shaft 230231. Such an arrangement allows pierceable seal 23056 and piercing member guide 230237 to translate into housing 23052 together, at least during a portion of translation of seal barrier 23056C. In addition, pierceable seal 23056 can be removably attached to piercing member guide 230237 by a variety of means known in the art such as, for example, removable quick-release fitting coupling, or can be configured to allow contact between components to guide translation of seal barrier 23056C onto piercing member 230233. When a piercing member guide, such as piercing member guide 230237 in Figure 144A, is used, the piercing member guide may be translated with pierceable seal 23056, during at least part of the translation, to ensure that the barrier 23056 C seal contact and pierce through piercing member 230233. Once the fluid path is opened or connected, translation of plunger seal 230 160 in the distal direction by the action mechanism causes drug chamber 23021 to be forced through the sterile fluid connector. In some embodiments, a needle insertion mechanism, as described herein, may be connected to the other end of fluid conduit 23035 to insert a needle into the user's body to facilitate fluid transfer to the user.
The embodiment shown in Figure 144A also comprises plunger seal 260, which can be used as part of the status indication mechanism in conjunction with piercing member guide 237. More specifically, in this embodiment plunger seal 260 includes interface / contact 261 and the corresponding interface / contact 262 is located on piercing member guide 237. When the plunger seal 260 and piercing member guide 237 reach the proximity of the supply end (for example, as in Figure 144C), the interconnect / contact 261 and the interconnect / contact 261 interconnect and transduce a noticeable signal to the user.
The new embodiments presented herein provide sterile fluid path connections and integrated fluid containers, and fluid pumps using such connections, which are configured to maintain sterility of the fluid path before, during, and after of device operation, and which enable active security controls for the device. Integration of the fluid path connector into a part of the fluid container helps to ensure the integrity and sterility of the fluid path container. In addition, by integrating the sterile fluid path connector into a part of the fluid container, the connection for fluid transfer can be controlled by the user (i.e., user activated) and enabled by the action mechanism function . Therefore, the user activation stages and the internal operation of the fluid pump can be greatly simplified by the new sterile fluid path connections
277 integrated of the present embodiments.
In another embodiment, the fluid container comprises at least two internal, movable compartments, where each compartment-compartment interface comprises a distinct pierceable seal capable of being altered by the piercing member of the sterile fluid path connector to create sterile fluid communication between the path of sterile fluid and that compartment of the sterile fluid container. As shown in Figure 145, container 23050 may use one or more seals in addition to plunger seal 230160 and pierceable seal 230156. This may be applicable, for example, when multiple fluid substances are desired to be delivered through the container and device. infusion pump. Figure 145 shows one such embodiment that uses two additional seals, 230263 and 230165, to create the compartments or chambers 230121A, 230121B and 230121C, within which one or more fluid substances can be stored for delivery. The embodiment of Figure 145, the pierceable seal 230156 includes the seal barrier 230156C and the base 230156A, base 230156A which is adjacent to the barrel edge 23058A on its distal side and the connector shaft 230131A on its proximal side, the supports of which they are kept within the housing 23052. The connector shaft 230151 further includes the vacuum port 230131B, with a channel leading to the sterile chamber 23032. Connector shaft 230131 is also configured with conduit port 230131D, which provides outlet for connector 230130 for sterile fluid to the rest of the infusion device (eg, an injection mechanism). The conduit port 230131D and the vacuum port 230131B may each contain a membrane, filter, or seals, such as one-way seals, that allow fluid to flow out of chamber 23032 through the respective ports but do not allow fluid flows into chamber 23032 through these ports. In addition, or alternatively, the conduit port 230131D and the vacuum port 230131B may be plugged at certain points in the assembly or operation. For example, vacuum port 230131B can be used to evacuate sterile cavity 32 during fabrication, assembly, or at any point prior to device operation; and then vacuum port 230131B can be plugged after evacuation is complete.
Upon activation of the fluid pump, pressure at interface 230168 of plunger seal 230160 causes distal translation of plunger seal 230160 into housing 23052. The pneumatic and / or hydraulic pressure within the fluid substance or substances held in the chambers 230121 A, 230121B and 230121C of drug transmits the force to, and causes distal translation of, the chamber seal 230163, the chamber seal 230165, and pierceable seal 230156, causing seal barrier 230156C to translate into housing 23052 and be pierced by piercing member 230133. This enables the sterile fluid path connection to be created or opened, as described herein. After further translation of the plunger seal 160, the fluid substance held in the chamber 230121A of
278 Mutable drug is dispensed through conduit 230135. After further translation of fluids and seals, seal 230165 can then be pierced by piercing member 230133, thereby allowing the fluid substance in chamber 230121B of mutable fluid is dispensed from the fluid path connector. If additional compartments or chambers are desired, more seals and chambers (such as seal 230163 and mutable chamber 230121C) can be configured, and then coupled in the same way until piston seal 230160 has fully moved into casing 23052 This configuration can offer advantages over single compartment fluid containers. For example, a diluent can be stored in mutable fluid chamber 230121A and a therapeutic drug can be stored in mutable fluid chamber 230121B, such that the sterile fluid path is first purged by the diluent prior to delivery of drug therapy to the patient. When combinations of drugs are desired for delivery, multiple therapeutic agents can be stored and delivered using the configuration provided by the present embodiment. Any number of seals and drug chambers can be used in such a configuration provided that the piercing member 230133, the mechanism of action, and the other components of the embodiments are configured appropriately for such delivery.
The new integrated sterile fluid path connectors of the present invention may further incorporate status indication into fluid delivery mechanisms. Such status indication features can be incorporated into the action mechanism 23090, as described in WO 2013033467. In addition, or alternatively, status indication features can be incorporated into the components of the fluid path connectors. sterile. In one embodiment, one or more interconnects are contained within, or proximal to, the plunger seal. At the end of the fluid supply, the piercing member can be used to contact, or as a contact for, the interconnect to open, close, or otherwise create a signal in the power and control system to provide feedback to the user. In another embodiment, one of the interconnects / contacts is contained within, or proximal to, the plunger seal, while the other is contained within or distal to the pierceable seal, such as in or on a seal mounting or guide piece. At the end of the fluid supply, the interconnects and corresponding contacts close enough to allow a signal to be sent to the power and control system to provide feedback to the user.
In another embodiment, the connector shaft surface sequestered in the sterile chamber 23032 can incorporate, or can itself be used as, a contact or interconnect for the status indication mechanism. For example, an end of supply signal can be provided using a spring or flex arm / leaf type switch mechanism.
279 Contained within sterile 23032 compartment, coupled to the surface of the connector shaft and connected through the shaft to the appropriate electronics. In this arrangement, in the non-pressurized state (prior to device activation), the switch is in the open position, and there is no contact / interconnect or transduced signal. When the device is activated, i.e. when the action engages the plunger seal within the drug container, pneumatic and / or hydraulic pressure causes the pierceable seal to move to the piercer member, thereby altering the pierceable seal and allowing fluid to flow through the sterile fluid connector. Pneumatic and / or hydraulic pressure also causes the septum of the perforable seal to press against the switch mechanism until it interconnects with its complementary contacts, which closes the circuit and allows a signal to be transduced to the user, indicating that the drug supply. At the end of the supply, the pneumatic and / or hydraulic pressure inside the sterile chamber is released and the switch opens again, breaking the circuit and providing an end of supply signal to the user.
Such a configuration, in which the connector shaft surface sequestered in the sterile chamber of the sterile fluid path connector can incorporate, or be used by itself as, a contact or interconnect for the status indication mechanism, can be provided by a pierceable seal configuration. For example, as shown in Figure 146A through Figure 146E, fluid chamber 23058 comprises a plunger seal 230160, configured to engage an action mechanism that forces plunger seal 230160 toward sterile fluid connector 230130. In the initial position (i.e., before the action is engaged), the pierceable seal 230356 maintains the sterile chamber 23032 within the space defined by the pierceable seal 230356 and the connector shaft 230131, particularly as partially supported by the 230134 mount. seal, as shown in Figure 146A. Connector shaft 230131 further includes piercing member 23033, and vacuum port or discharge 131 B in which the sterility of chamber 23032 is maintained by filter 23039. Connector shaft base 230131A, sealing member 230356A of pierceable member 230356, and barrel edge 23058A are all secured to housing 23052, which housing may be a plug such as a crimped plug. Connector shaft 230131 also includes outlet port 230131D, which provides an outlet passage for fluid conduit 23035 from the sterile fluid path connector. Once the action of the pump is activated and the plunger seal 230160 is forced into the piercing member 23033, the pneumatic and / or hydraulic pressure within the mutable fluid chamber 23021 forces the piercing seal seal barrier 230356C to the member Perforator 23033, which pierces the seal barrier 230356C and opens the sterile fluid path. Continued pneumatic and / or hydraulic pressure within mutable chamber 23021 forces at least a portion of pierceable seal 230356 to contact at least a portion of connector shaft 230131 within sterile chamber 23032, as shown in Figure 146B.
280
This continued pneumatic and / or hydraulic pressure, as long as the action is activated and the fluid remains in the movable chamber 23021, maintains contact between the seal 230356 and the connector shaft 230131, as shown in Figures 146C and 146D. When the fluid has been pumped out of the mutable fluid chamber 23021, such that this chamber basically no longer exists, the pneumatic and / or hydraulic pressure against the 230356 seal is released, and the 230356 seal returns to a non-state. pressurized into chamber 23032, where there is no longer contact between seal 230356 and shaft 230131, as shown in Figure 146E.
This aspect of the embodiments is advantageous for a variety of devices and configurations useful for providing a sterile fluid path connector with at least one sensor configured to indicate the status of fluid transfer from the sterile fluid container to the connector. An example of such a sensor is a switch mechanism contained within the sterile chamber in the sterile fluid connector. For example, in the embodiment shown in Figure 147A through Figure 147H, fluid container 230350 includes barrel 230358, which houses fluid chamber 230321 and piston seal 230360, configured to engage an action mechanism that forces plunger seal 230360 and fluid in mutable fluid chamber 230321 into sterile fluid connector 230330. Pierceable seal 230356 maintains sterile chamber 230332 within the space defined by pierceable seal 230356 and connector shaft 230331, as shown in Figure 147A and Figure 147B, where the fluid path is closed. Connector 230330 further includes connector shaft 230331, further including vacuum port 230331B, wherein chamber sterility 230332 is maintained by filter 230339; outlet port 230331D, which provides an outlet passage for fluid conduit 230335 from sterile fluid path connector 230330; and engages piercing member 333. The connector shaft base 230331A, the pierceable seal 230356, the sealing member 230356A, and the barrel edge 230358A are secured to the housing 230352. The connector shaft 230331 further houses, in the sterile chamber 230332, the ring marked 230391 fitted to seal mount 230334 on connector shaft 230331; contact 230392; spring 230393; and interconnects 230362 that are in communication with flexible power strip 238394 (flex). As shown in Figure 147A and Figure 147B, in the initial state prior to action activation, spring 230393 rests in an uncompressed state, and contact 230392 is maintained between spring 230393 and the ring marked 230391 at a position where there is no contact between interconnects 230362 and contact 230392. Contact 230392 is further stabilized within sterile chamber 230332 by the position of piercing member 230333 passing through contact 230392 through passage 230392C.
As shown in Figure 147C and Figure 147D, once the action mechanism is activated and plunger seal 230360 is forced into piercing member 230333, as
281 indicates by the arrow, the pneumatic and / or hydraulic pressure within the mutable fluid chamber 230321 forces the seal barrier 230356C of the pierceable seal 230356 into the perforator member 230333, thereby piercing the seal barrier 230356C and opening the path of sterile fluid in such a way that fluid can pass into sterile fluid line 230335. This pneumatic and / or hydraulic pressure within the movable chamber 230321 also forces at least a part of the barrier seal 230356C against at least a part of the contact 230392, in such a way that the spring 230393 is compressed until the contact 230392 is with the interconnections 230362 inside the sterile chamber 230332, forming an interconnection. A signal can then be transduced through contact 230392, interface 230362, and flex 230394. Continuous pneumatic and / or hydraulic pressure (see arrow), provided that the action is activated and the fluid remains in the mutable chamber 230321, compresses the spring 230393 and maintains contact between the seal 230356, the contact 230392 and the interconnection 230362 , in such a way that the interconnection continues, as shown in Figure 147E to Figure 147F. When fluid has been pumped out of mutable fluid chamber 230321, such that this chamber basically no longer exists and flow through sterile fluid connector 230330 has ceased, as shown in Figure 147G and Figure 147 H (the latter is a different sectional view of the sterile fluid path connector showing the position of the interconnects 230362 within the connector shaft 230331), the pneumatic and / or hydraulic pressure against the seal 230356 is released, and spring 230393 returns to the uncompressed state, pushing contact 230362 back toward the ring marked 230391 and breaking the interconnection between contact 230392 and interconnection 230362. Once this interconnection is broken, the signal is no longer transduced through of flex 230394.
Other switch mechanisms can be designed that use the position of the membrane in the pressurized and non-pressurized states to facilitate signal transduction to indicate the status of fluid transfer from the sterile fluid container to the connector. For example, as shown in Figure 148A through Figure 148G, connector shaft 230331 can accommodate components of a switch comprising leaf / flex arm contacts 395. Figure 148B, Figure 148D, and Figure 148E show the sterile fluid path connector in the pre-use position, where pierceable seal 230356 is undrilled and intact. In this position, contacts 230395 do not touch (or are in close enough proximity to) interconnects 230362, and no signal can be transduced. Figure 148C, Figure 148F and Figure 148G show the sterile fluid path connector in the activated, pressurized position, where the pneumatic and / or hydraulic pressure of the fluid chamber has deformed the barrier seal 230356C piercing member 230333, piercing pierceable seal 230356 and opening the fluid path. In this position, the barrier seal 230356C has also been forced against the 230395 contacts in such a way that the
282 Contacts 230395 find (or are in fairly close proximity to) the interconnects 230362, such that the interconnect forms a signal that can be transduced through bending 230394. Figures 148D and 10F are perspectives (where the barrel and housing are not shown), which illustrate the positions of the pierceable seal 230365, the connector shaft 230331, and the piercer member 230333 in the preused and pressurized positions, respectively. Figures 148E and 148G are perspectives in which the barrel, housing, and pierceable seal are not shown, to illustrate the positions of the 230395 contacts and the 230362 interconnects in the preuse (no interconnect) and pressurized (interconnected) positions, respectively.
FIG. 149A and FIG. 149D further illustrate an embodiment in which the blade / arm contacts 230395 do not interconnect with interconnections 362 until and unless, as shown in FIG. 149B and FIG. 149D, the pneumatic pressure and / or hydraulic force seal barrier 230356C onto connections 230395, which force is then transferred to bring contacts 230395 into contact with interconnects 230362, which then allows signal flow through flex 230394. In addition, as shown in the embodiment of Figure 149A to Figure 149D, connector shaft 230331 further includes internal post 230334A, a position-limiting structure. of contacts 230395 and membrane 230356 to avoid an over-centered position that could interfere with the passage of fluid through the sterile fluid path connector.
Figure 12A to Figure 12D further illustrate an embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector. Figure 150B illustrates the position of the components of a sterile fluid connector 230330 in an unpressurized state, while Figure 150C illustrates the pressurized state and Figure 150D illustrates an end of supply state. The interconnect with interconnects 230362 and the contact or contacts 230395 are located within the sterile chamber 230332 between the connector shaft 230331 and the perforable seal 230356, such that after the perforable seal 230356 is punctured, the pressure continued within of the drug chamber 230321 causes the interconnection between one or more interconnects 230362 and one or more contacts 230335, which transmits a signal to the user, and whose signal is terminated once the pressure inside the drug chamber 321 decreases and the interconnection is lost, that is, at the end of supply. A variety of known interconnections and contacts can be used with the present embodiments, which will be readily understood by one of ordinary skill in the art. For example, a variety of: Hall effect sensors; magnetic field sensors or giant magnetoresistance (GMR); optical sensors; capacitive or capacitance change sensors; ultrasonic sensors; and linear travel sensors, LVDT, linear resistive, or radiometric linear resistive; and
283 combinations thereof, which are capable of coordinating to transmit a signal to the user. Figure 151A to Figure 151 C illustrate another embodiment of a sterile fluid connector capable of transmitting a signal indicating the status of fluid transfer from the sterile fluid container to the connector.
Yet another switch mechanism is shown in Figure 152A and Figure 152B, showing the sectional and isometric sectional views of a sterile fluid path connector (barrel not shown). In this embodiment, the sterile chamber 230332, defined in part by the position of the pierceable seal 230356, the seal mount 230334, and the shaft connection 230331. The connector shaft also houses piercing member 230333 and interconnects 230362 within sterile chamber 230332. The switch mechanism includes interconnects 230362, a first compression spring 230393, a contact 230392, and a second compression spring 230396. In this embodiment, shown in the de-pressurized, de-energized state, both compression springs 230393 and 396 are compressed in order for contact 230392 to interconnect with interconnects 230362. Before and after the release of the pneumatic and / or hydraulic pressure against the seal barrier 230356, the compression springs 230393 and 230396 decompress and the interconnection breaks.
Another embodiment of a switch mechanism is shown in Figure 153A and Figure 153B. In this embodiment, the perforable seal 230456 comprises a conductive material or coating. Connector shaft 230431 includes rib 434A, a structure that ensures continuity between conductive pierceable seal 230456 and contacts 230462 is broken when system pressure drops at the end of the fluid supply. More specifically, as shown in Figure 151B, in the pressurized system in which pneumatic and / or hydraulic pressure has caused the conductive pierceable membrane 230456 to be altered by piercing member 230433, the conductive pierceable membrane 230456 must be deformed also proximal to the nerve 230434 in order to find the interconnections 230462. Once the pneumatic and / or hydraulic pressure ceases, that is, at the end of the fluid supply, the conductive pierceable membrane 230456 is naturally released from the proximal interconnection to the rib 230434.
Yet another embodiment of a switch mechanism is shown in Figure 154. In this embodiment, the connector shaft 230531 comprises the conductive elastomer 230597 held in the sterile chamber 230532 between the connector shaft 230531 and the pierceable membrane 230556. In this embodiment, at least a portion of the conductive elastomer 230597 is attached to or otherwise engaged with the seal assembly 230534, and is configured with a centrally located opening to allow the Barrier seal 230556C to be forced into contact with the perforating member 230533 upon activation of the pump and the creation of pneumatic and / or hydraulic pressure against the perforable membrane 230556. The elastomer
284 Conductive 230597 is elastic in nature and can be deformed (ie stretched) in response to the distal force of the pierceable seal 230556, thereby deforming to find the interconnections 230362 under the pressure of the pierceable seal 230356. The elastomeric nature of the conductive elastomer 230597 allows it to return to the pre- formation state, where no interconnect exists, in a non-pressurized environment. Therefore, once the pneumatic and / or hydraulic pressure ceases, that is, at the end of supply, the conductive elastomer film 230597 is passively released from contact with the interconnections 230562, and the signal is interrupted.
In another embodiment, shown in Figure 155, the sterile fluid path connector includes a sensor mechanism comprising the dome switch 230666, which dome is made of or includes conductive material such that the 230666 dome switch The dome can act as a contact to create a signal when the dome switch 230666 meets, or moves close enough to, the 230662 interconnects to complete the circuit. Dome switch 230666 is configured with at least one outer part 230666A that resists deformation and mates with or is supported on the inner wall of connector shaft seal mount 230634. Alternatively, the deformation resistant outer portion of the dome switch may be a radial ring, or any structure that stabilizes the position of the dome within the sterile fluid path connector. The conductive part of the dome switch may comprise memory alloy so that it resembles its dome shape, but can be deformed into a flatter shape under pressure, then returning to the dome shape once the pressure is relieved. In the embodiment of Figure 155, dome switch 230666 further comprises opening 230666 C through which piercing member 230633 can pass through when dome switch 230666 is pressed in the direction of interconnects 230662. More specifically, when the pump device is actuated and pneumatic and / or hydraulic pressure builds up against the pierceable membrane (not shown), the pierceable membrane is forced onto piercing member 230633 and altered to open the fluid path. Dome switch 230666 is similarly deformed by pneumatic and / or hydraulic pressure or by distal pressure of the deformed portion of the pierceable seal supported thereon, and dome switch 666 flattens toward interconnects 230662 to allow a signal to be transduced. Once the pneumatic and / or hydraulic pressure stops, that is, at the end of supply, the dome switch returns to its pre-deformation dome shape and interconnection ceases. As shown in Figure 155, the dome switch 230666 is configured for placement below the pierceable seal (not shown), within the sterile cavity of the fluid path connector. However, the dome switch could be configured to mount on top of the pierceable seal, and after
285 Pressurization would be pushed in close enough proximity to the 230662 interconnects to generate a signal. Alternatively, the dome switch could be made of uniformly deformable / resilient shape memory material with the conductive part of the dome switch configured on the outside or edge of the dome, and placed upside down (like a bowl shape) in the sterile chamber of the fluid path connector. In this configuration, pneumatic and / or hydraulic pressure against the perforated pierceable membrane would sufficiently flatten the dome until the outer conductive portion of the dome made sufficient contact with the interconnects located on the connector shaft to allow a signal. After the pressure ceases, that is, at the end of delivery, the dome would return to its remembered dome shape, thereby removing the connector contacts from the interconnect.
As should be clear from the foregoing discussions, a variety of interconnects and contacts, or similar components, are known in the art and can be used in the new embodiments disclosed herein. As will be readily understood by one skilled in the art, a wide variety of magnets, sensors, coils, and the like can be used to connect, transmit, or retransmit a signal for user feedback. Generally, any RLC circuit system that has a resistor, inductor, and electrical capacitor, connected in series or in parallel, can be used for this purpose. For example, Hall effect sensors can be used as interconnects; magnetic field sensors or giant magnetoresistance (GMR); optical sensors; capacitive or capacitance change sensors; ultrasonic sensors; and linear trip, LVDT, linear resistive, or radiometric linear resistive sensors and use the corresponding contacts to allow a signal to be sent to the power and control system to provide feedback to the user. The location of the contacts and interconnections can be interchanged or in a variety of other configurations that allow for the realization of an electrical circuit or otherwise allow for transmission between components. Through the use of one or more status switch interconnects and one or more corresponding electrical contacts, the state of the action mechanism can be transmitted before, during, and after operation to the power and control system to provide feedback to the user. Such feedback may be tactile, visual, or auditory, and may be redundant such that more than one signal or type of feedback is provided to the user during use of the device.
Furthermore, the embodiments of the present invention provide end-of-supply compliance to ensure that the full volume of fluid has basically been delivered and that the status indication features have been properly connected to provide accurate feedback to the user. Through these
286 mechanisms, confirmation of fluid supply to the user or administration can be accurately provided. Therefore, the new devices of the present invention improve one or more of the problems associated with the prior art devices. Optionally, the action mechanism may include one or more compliance features that allow for additional axial translation of the plunger seal, for example, to allow basically the full volume of fluid to be delivered and to ensure that the contact mechanisms have been connected feedback. For example, in one embodiment of the present invention, the actuation mechanism can be configured to drive additional axial translation of at least a portion of the plunger seal for a compliance push of the plunger seal, or of fluid, from the container of fluid. In addition, or alternatively, the plunger seal, by itself, may have some compressibility that allows for compliance thrust. For example, when an outlet piston seal is used, that is, a piston seal that is deformable from an initial state, the piston seal can be caused to deform or protrude to provide a compliance thrust. Similarly, the plunger seal can be porous, compressible, deformable, or the like to be capable of providing compliance thrust by itself.
As previously described, the location of the contacts and interconnects can be interchanged or in a variety of other configurations that allow for the realization of an electrical circuit or otherwise allow for transmission between components. In one embodiment, the plunger seal can incorporate, or can itself be used as, a contact or interconnect for the status indication mechanism (eg, 61 in Figure 142C). In one embodiment, the seal assembly can incorporate, or can be used by itself as, a contact or interconnect for the status indication mechanism (eg 62 in Figure 142C). In one embodiment, a guide part can incorporate, or can be used by itself as, a contact or interconnect for the status indication mechanism (eg, 232 in Figure 144A). In another embodiment, the proximal surface of the connector shaft sequestered in the sterile chamber 32 can incorporate, or can itself be used as, a contact or interconnect for the status indication mechanism (eg, Figure 147 to Figure 155).
Other components of the sterile fluid path connection can be used in a similar way for multiple functions. Alternatively, other optional components can be used in the new embodiments of the present invention. For example, one or more optional flow restrictors can be used in the fluid path connection configurations described herein. In at least one embodiment, a flow restrictor can be used in the connection between the piercing member and the fluid passage. The fluid pump is capable of supplying a variety of fluids with different viscosities and
287 volumes. The fluid pump is capable of supplying a fluid with a controlled flow rate (velocity) or a specified volume. In one embodiment, the fluid delivery process is controlled by one or more flow restrictors within the fluid path connection and / or the sterile fluid line. In other embodiments, other flow rates may be provided by varying the geometry of the fluid flow path or supply line, varying the rate at which a component of the action mechanism advances into the fluid container to dispense the fluid into the same, or combinations thereof. In at least one embodiment of the present invention, the connector shaft itself can be used as part of the fluid path and, optionally, can function as a flow restrictor.
It is to be understood from the foregoing description that the fluid path connections and fluid pumps disclosed herein provide an efficient and easy to operate system for automated fluid delivery from a fluid container. The new devices of the present invention provide container connections that maintain fluid path sterility and that are integrated into the fluid container, and fluid supply pumps that incorporate such integrated sterile fluid path connections into fluid containers. . Such devices are safe and easy to use, and are aesthetically and economically attractive to self-administering patients. The devices described in this document incorporate features that make it easy to activate, operate, and close the device even for untrained users. Because the fluid path is disconnected until fluid supply is desired by the operator, the sterility of the fluid path connection, the fluid container, the fluid, and the entire device are maintained. These aspects of the present embodiments provide highly desirable storage, transportation, and safety benefits for the operator. Furthermore, the new configurations of the fluid path connections and the drug pumps of the present invention maintain the sterility of the fluid path through the operation of the device. Because the path the fluid travels through the device is kept completely sterile, these components only need to be sterilized during the manufacturing process. Such components include the fluid container of the mechanism of action, the fluid path connection, the sterile fluid passage, and, when the fluid is a drug, the insertion mechanism. In at least one embodiment of the present invention, the power and control system, mounting platform, control arm, trigger mechanism, housing, and other components of the fluid pump need not be sterilized. This greatly improves the manufacturing capacity of the device and reduces associated mounting costs. Therefore, the devices of the present invention do not require final sterilization after completion of assembly. An additional benefit of the present embodiments is that the components described herein
288 they are designed to be modular in such a way that, for example, the fluid path connection and the other components of the device can be integrated into a housing and easily connected to function as a fluid pump.
The assembly or fabrication of the fluid path connection 23030 or any of the individual components can utilize a variety of materials and methodologies known in the art. For example, a variety of known cleaning fluids such as isopropyl alcohol and hexane can be used to clean components or devices. Similarly, a variety of known adhesives can be employed in the manufacturing process. In addition, known silicone or lubrication fluids and processes can be employed during the manufacture of the new components and devices. In addition, known sterilization processes can be employed in one or more of the manufacturing or assembly steps to ensure sterility of the final product.
The fluid path connection can be mounted in a variety of methodologies. In a mounting method, the sterile fluid path connection can be mounted, for example, as shown in Figure 143A and Figure 143B, and then joined, mounted, connected, or otherwise integrated into fluid container 23050 such that at least a portion of the pierceable seal 23056 is contained within the fluid container 23050. Fluid container 23050 can then be filled with fluid and capped with a plunger seal 23060 at an end opposite to pierceable seal 23056. Barrel 23058 can be filled with fluid through the open proximal end prior to insertion of the 23060 plunger seal from the proximal end of barrel 23058. The action mechanism 23090 can then be attached to the proximal end of the fluid container 23050 in such a way that a component of the action mechanism 23090 is able to contact the plunger seal 23060. Insertion mechanism 23070 can be mounted and attached to the other end of fluid conduit 23035. This complete subassembly, which includes the action mechanism 23090, the fluid container 23050, the fluid path connection 23030, the fluid passage 23035, and the insertion mechanism 23070, can be sterilized by known techniques prior to mounting on the drug delivery device 230100. Certain components of this subassembly can be mounted on a mounting platform inside the housing 12A, 12B or directly inside the housing 12A, 12B, while other components can be mounted on a guide, channel, or other component or aspect for activation by the user.
The manufacture of a fluid pump includes the step of attaching both the fluid path connection and the fluid container, either separately or in the form of a combined component, to a drug pump mounting platform or housing. The manufacturing method further includes attaching the action mechanism, the fluid container, and the insertion mechanism to the mounting platform or housing. Additional components of the pump
289 Fluids, as described above, which include the power and control system, the trigger mechanism, and the control arm can be attached, pre-formed, or pre-mounted on the mounting platform or housing. An adhesive patch and a patch liner can be attached to the surface of the drug pump casing that contacts the user during operation of the device.
A method of operating the fluid pump includes one or more of the following steps: activating the activation mechanism by the user; move a control arm to operate an insertion mechanism; activate an action control mechanism to push the plunger seal, connect the sterile fluid path connection and drive fluid flow through the fluid pump, where translation of the fluid path connection causes a seal pierceable is pierced by a piercing member whereby a fluid path is opened from the fluid container to the fluid path connection. The action control mechanism can be activated by actuation of a power and control system. The method may further include the step of: attaching a sensor to the optional body prior to activating the trigger mechanism. In addition, the method of operation may include moving a plunger seal with the action control mechanism and the fluid container to force the flow of fluid drug through the fluid container, the fluid path connection, a fluid line. sterile and, optionally, the insertion mechanism for supplying the fluid to a user's body.
XXIII. Additional embodiments of the mechanism of action
At least some of the drug delivery devices described in the present application, including at least those described in relation to Figures 1-56 and 74-157B, can be configured to incorporate the mechanism of action embodiments that they are described later in relation to Figures 156-157B. The embodiments of the mechanism of action described below in relation to Figures 156-157B can be used to replace, in whole or in part, the mechanisms 100, 500, 1000, 2100, 10100 of action described above, or any other mechanism of action described in this document, where appropriate.
In general, the present embodiments provide mechanisms of action with integrated status indication, drug delivery devices incorporating such mechanisms of action, methods of operation of such devices, and methods of mounting such devices. The mechanisms of action of the present disclosure provide integrated status indication features that provide feedback to the user before, during, and after drug delivery. For example, an initial feedback can be provided to the user to identify that the system is operational and ready for drug delivery. After activation, the system can
290 then provide one or more indications of drug delivery status to the user. At the end of the drug delivery, the mechanism of action and the drug delivery device can provide an indication of end of dose. When the end of dose indication is linked to the piston reaching the end of its axial translation, the action mechanism and drug delivery device provide a true end of dose indication to the user. In addition, the embodiments of the present disclosure provide end-of-dose compliance to ensure that the full drug dose has basically been delivered to the user and that the status indication features have been properly connected to provide accurate feedback to the user. Through these mechanisms, confirmation of drug dose delivery can be accurately provided to the user or administrator.
In at least one embodiment, the present disclosure provides an action mechanism having an integrated status indication including: an action housing, a status switch interconnect, an action matching member, a piston, and a drug container It has a stopper, a pierceable seal, a barrel, and a plunger seal. The action matching member can be configured to be supported on a piston interface surface. The drug container may preferably contain a drug fluid for delivery to the user. The action mechanism may further include a connection mount attached to the pierceable seal. A cover sleeve can be used between the action matching member and the interface surface of the piston to provide, for example, a more even distribution of force from the matching member to the piston. A contact sleeve can be slidably mounted to the action housing through an axial opening in the action housing, such that the hooks of the sleeve at a distal end of the contact sleeve are made to contact the piston between the interface surface and a contact protrusion near the proximal end of the piston. The piston may also include a locking groove, between the contact protrusion and the proximal end of the piston. The contact sleeve may have a radially extending ring at its proximal end, on which one or more flexing tips reside.
The mechanism of action may further include one or more contact surfaces located on the corresponding components. Such contact surfaces may be electrical contact surfaces, mechanical contact surfaces, or electromechanical contact surfaces. Such surfaces may initially be in contact and cause them to disengage, or be initially disconnected and cause them to engage, to allow a signal to be sent to and / or from the power control system. In at least one embodiment, as further described herein, the contact surfaces may be electrical contact surfaces that are initially disconnected and caused to enter
291 in coupling whereby, after such coupling, the contact surfaces are capable of continuing an energy path or otherwise transmitting a signal to the energy and control system. In another embodiment of the present disclosure, the contact surfaces are mechanical contact surfaces that are initially in contact and are caused to disengage whereby, upon such decoupling, such decoupling is communicated to the power and control system. Such signals can be transferred through one or more interconnections to the power and control system or by mechanical action to the power and control system. Such components can be used in the action mechanism to measure and transmit information related to the state of operation of the action mechanism, which can be converted by the power and control system into tactile, auditory, and / or visual feedback to the user. . Regardless of the electrical or mechanical nature of the contact surfaces, the movement of the components that enables the transmission of a signal to the power and control system is enabled by a matching member that axially translates a contact sleeve in the distal direction during device operation.
The actuation mechanism may include a slidingly mounted piston extension at a distal end and within a passage through axial piston; a piston extension matching member, which is mounted within the piston axial through passage and is initially compressed between the piston extension and the piston; and, optionally, a piston matching member bracket between the piston extension matching member and the piston extension. The piston extension is retained within the piston by interaction between one or more piston extension extension arms and one or more corresponding piston connection grooves. The piston extension can be used to perform a compliance push of the drug fluid from the drug container. In addition, or alternatively, the mechanism of action may utilize a compressible plunger seal, where such compression capacity or distance allows for a compliance push of the drug fluid from the drug container. Other compliance features are further described in this document.
In another embodiment of the present disclosure, an action mechanism having an integrated incremental status indication includes an action housing, an action matching member, a piston, an incremental status stem having a mounted, attached stem interconnect , printed, or otherwise attached thereto, and a drug container having a stopper, a pierceable seal, a barrel, and a plunger seal, where the incremental state stem resides within the axial through passages of the action housing and the piston. The incremental state stem may have one or more interconnects that contact one or more contacts on the piston to provide incremental state feedback to the user. Incremental state realization can similarly use the
292 electrical, mechanical, or electromechanical interconnections and contacts, and / or one or more of the compliance characteristics, as described above.
In a further embodiment, the present disclosure provides a drug delivery device with integrated status indication. The drug delivery device includes a housing and mounting platform, on which an activation mechanism, an insertion mechanism, a fluid path connection, a power and control system, and an action mechanism can be mounted. it has a drug container. The action matching member can be configured to be supported on a piston interface surface. The drug container may preferably contain a drug fluid for delivery to the user. The action mechanism may further include a connection mount attached to the pierceable seal. A cover sleeve between the action matching member and the interface surface of the piston can be used, for example, to provide a more even distribution of force from the matching member to the piston. A contact sleeve can be slidably mounted in the action housing through an axial opening in the action housing in such a way that the sleeve hooks at a distal end of the contact sleeve are made to contact the piston between the interface surface and a contact protrusion near the proximal end of the piston. The piston may also include a locking groove, between the contact protrusion and the proximal end of the piston. The contact sleeve may have a radially extending ring at its proximal end, on which one or more flexing tips reside. The mechanism of action may further include one or more contact surfaces located on the corresponding components. Such contact surfaces can be electrical contact surfaces, mechanical contact surfaces, with electromechanical contact surfaces. Such surfaces may initially be in contact and cause them to disengage, or they may be initially disconnected and cause them to engage, to allow a signal to be sent to and / or from the power control system. In at least one embodiment, as further described herein, the contact surfaces may be electrical contact surfaces that are initially disconnected and brought into engagement whereby, after such engagement, the contact surfaces are able to continue an energy path or otherwise transmit a signal to the power and control system. In another embodiment of the present disclosure, the contact surfaces are mechanical contact surfaces that are initially in contact and are caused to decouple whereby, after such decoupling, such decoupling is communicated to the power and control system. Regardless of the electrical or mechanical nature of the contact surfaces, the movement of the components is allowed, allowing the transmission of a signal to the energy control system by
293 a matching member that axially translates a contact sleeve in the distal direction during operation of the device.
In yet another embodiment, the present disclosure provides a drug delivery device with an incremental status indication. The drug delivery device includes a housing and a mounting platform, on which an activation mechanism, an insertion mechanism, a fluid path connection, a power and control system, and an action mechanism can be mounted. having a drug container, and further including an incremental state stem having a stem interconnect mounted, clamped, printed, or otherwise attached thereto, where the Incremental state stem resides within the axial through passages of the action housing and the piston, and where the Incremental state stem has one or more interconnects that contact one or more contacts on the piston to complete a transmission to the power and control system to provide incremental feedback to the user. The incremental status indication drug delivery device may similarly utilize the electrical, mechanical, or electromechanical interconnects and contacts, and / or one or more of the compliance features, as described above.
The present disclosure further provides a mounting method. The drug container can be mounted first and refilled with a drug fluid. The drug container includes a stopper, a pierceable seal, a barrel, and a plunger seal. The pierceable seal can be fixedly attached between the cap and the barrel, and a distal end of the barrel. The barrel can be filled with a drug fluid through the open proximal end prior to insertion of the plunger seal from the proximal end into barrel 58. An optional connection mount can be mounted on a distal end of the pierceable seal. The connection mount guides the insertion of the piercing member of the fluid path connection into the barrel of the drug container. The drug container can then be mounted on a distal end of the action housing.
Before mounting the drug container to the housing, a switch status interconnect can be mounted to a proximal end of the action housing. A contact sleeve, which has one or more sleeve hooks at a distal end and a ring at a proximal end that has an electrical contact thereon, can be mounted to the action housing through a passage through axially from the proximal end of the action housing. An action matching member can be inserted into a distal end of the action housing. Optionally, a cover sleeve can be inserted into a distal end of the action housing to basically cover the matching member. A piston can be inserted into the distal end of the action housing and through an axial pass through of the contact sleeve, such that a piston contact protrusion
294 is proximal to the sleeve hooks of the contact sleeve. The piston and action matching member, and an optional cover sleeve, can be compressed into the action housing. Such an assembly positions the action matching member in a compressed, energized initial state and preferably places a piston interface surface in contact with the proximal surface of the plunger seal at the proximal end of the barrel. When a piston extension is employed, the piston extension and the piston extension matching member, and an optional piston matching member holder, can be compressed in one pass through axial piston prior to compression of the components. Before, or after, these components are installed in the action mechanism housing, a primary container can be attached.
When one or more interconnects or contacts are used for status indication, such components can be mounted, connected, printed, or otherwise attached to their corresponding components prior to mounting such components on the actuation mechanism. When a separate incremental state stem and a corresponding stem interconnect are used for such an incremental status indication, the stem interconnect can be mounted, clamped, printed, or otherwise bond to the incremental status stem prior to mounting the incremental status stem at the proximal end of the contact sleeve and / or the proximal end of the actuation housing such that the incremental status stem reside within one pass through axially of the contact sleeve and the action housing. The incremental state stem is further mounted to reside within a passage through axially through the piston.
The disclosure describes, in one aspect, a drug delivery device mechanism of action for use in cooperation with a drug container that includes a plunger seal. The actuation mechanism has an axis including an actuation housing, a piston adapted to impart movement to the plunger seal within the drug container, a plurality of matching members arranged in parallel, and a retainer. The piston is arranged to move from a first retracted position along the axis to a second extended position. The fitness members are adapted to move from a first energized position to a second non-energized position as a result of the release of energy. The matching members are arranged to cause movement of the piston from the first retracted position to the second extended position when the matching members move from the first energized position to the second non-energized position. The retainer is arranged to hold the adequacy members in the first energized position when the retainer is in a first detent position, and to release the adequacy members from the first energized position when the retainer is moved to a second release position.
295
In at least one embodiment, the plurality of matching members includes at least one of a tension spring or a compression spring. In at least one embodiment, the plurality of matching members includes a pair of springs, in at least one embodiment of which the springs are compression springs. In at least one embodiment, the compression springs are arranged concentrically, and are arranged around at least a portion of the piston. In at least one embodiment, the retainer engages at least a portion of the piston to retain the piston in its retracted position when the retainer is in its first retention position. At least one embodiment further includes a sleeve assembly arranged around at least one of a plurality of fit members. In at least one embodiment, the sleeve assembly includes a plurality of telescopic sleeves, and the sleeve assembly is arranged to move axially with the piston. At least one embodiment further includes at least one window and at least a portion of the sleeve assembly is visible through the window with at least a portion of the sleeve assembly being visible through said window until the piston is in a second position. extended. At least one additional embodiment includes an end of dose indicator arranged basically adjacent to the window, the end of dose indicator being adapted to identify at least one of when the sleeve assembly is arranged underlying the window and when the sleeve assembly is not is arranged underlying the window, the relative movement of the sleeve assembly with reference to the window or other reference component, stopping such movement, and the rate or change of rate of movement. In at least one embodiment, the end-of-dose indicator includes a sensor arranged to detect at least one of when the sleeve assembly is disposed underlying the window and when the sleeve assembly is not disposed underlying the window. In at least one embodiment, the sensor is a mechanical sensor, an electrical sensor, an ultrasonic sensor, a capacitive sensor, a magnetic sensor, or an optical sensor, in at least one embodiment, the sensor is a mechanical sensor arranged to be supported against the sleeve mount when the sleeve mount is arranged underlying the window.
In another aspect of the disclosure, a drug delivery device action mechanism is provided for use in cooperation with a drug container including a plunger seal; the action mechanism has a shaft and includes an action housing, a piston adapted to impart movement to the plunger seal within the drug container, at least one matching member, a retainer, a sleeve mount, and an end indicator dose. The piston is arranged for movement from at least a first retracted position to a second extended position along said axis. The at least one fitness member is arranged and adapted to move from a first energized position to a second non-energized position as a result of the release of energy.
296
The matching member is arranged to cause movement of the piston from the first retracted position to the second extended position when the matching member moves from the first energized position to the second non-energized position. The retainer is arranged to hold the adequacy member in the first energized position when the retainer is in a first detent position, and to release the adequacy member from the first energized position when the retainer is moved to a second release position. The sleeve mount adapts to move along the axis with the piston. The sleeve assembly is disposed at least partially within the action housing, and at least a portion of the sleeve assembly is visible through a window in the housing when the piston is in one of the first retracted or second position extended. The sleeve assembly is not visible through said window when the piston is in the other of the first retracted position or the second extended position. The end of dose indicator is basically arranged adjacent to the window. The end-of-dose indicator is adapted to identify at least one of when the sleeve assembly is disposed underlying the window and when the sleeve assembly is not disposed underlying the window.
In at least one embodiment, the sleeve assembly is disposed around the at least one matching member and includes a plurality of telescopic sleeves. In one embodiment, the sleeve assembly is disposed around the matching member or members. In at least one embodiment, the at least one matching member includes a plurality of matching members. A particular embodiment includes at least two compression springs arranged in parallel. In at least one embodiment, the end of dose indicator includes a sensor arranged to detect at least one of when the sleeve assembly is disposed underlying the window and when the sleeve assembly is not disposed underlying the window. In at least one embodiment, the sensor is at least one of a mechanical sensor, a mechanical sensor, an electrical sensor, an ultrasonic sensor, a capacitive sensor, a magnetic sensor, or an optical sensor. In a particular embodiment, the sensor is a mechanical sensor arranged to be supported against the sleeve mount when the sleeve mount is arranged underlying the window. In some embodiments, at least a portion of a distal end of the piston is adapted to dispose within the drug container when the piston is disposed in the first retracted position and the drug delivery system device action mechanism is disposed for use in cooperation with the drug container.
At least some embodiments of the present disclosure provide the force of action necessary to push a plunger seal and a drug fluid into a drug container, while reducing or minimizing the footprint of the action mechanism or the device as a whole. . Therefore, the present disclosure may provide a
297 mechanism of action that can be used within a more compact drug delivery device. Some embodiments of the present disclosure can be similarly used to provide additional strength, when needed for highly viscous drug fluids or for larger volume drug containers.
In accordance with another aspect of the disclosure, a drug delivery device action mechanism is provided for use in cooperation with a drug container including a plunger seal and a power and control system. The action mechanism includes an action housing, a piston, at least one matching member, a retainer, a sleeve mount, and an end of dose indicator. The action housing includes a shaft, and the housing further includes at least one window. The piston is arranged for movement from at least a first retracted position to a second position extended along the axis. The piston is also adapted to impart movement to the plunger seal within the drug container. The at least one fitness member is arranged and adapted to move from a first energized position to a second non-energized position as a result of the release of energy. The matching member is also arranged to cause movement of the piston from the first retracted position to the second extended position when the matching member moves from the first energized position to the second non-energized position. The retainer can be moved between a first retention position and a second release position. The retainer is arranged to hold the adequacy member in the first energized position when the retainer is in the first detent position, and to release the adequacy member from the first energized position when the retainer is moved to the second release position. The sleeve mount is disposed at least partially within the action housing. At least part of the sleeve assembly is adapted to move along the axis with the piston. At least a portion of the sleeve assembly is visible through the window when the piston is in one of the first retracted or second extended position, and the sleeve assembly is not visible through the window when the piston is in the other from the first retracted position or the second extended position. The end of dose indicator includes at least one switch interconnect, at least a portion of which is arranged substantially adjacent to the window and is adapted to identify at least one of when the sleeve assembly is disposed underlying the window and when The sleeve mount is not arranged underlying the window. The switch interconnect includes a mechanical trigger adapted to engage the sleeve mount through the window. The switch interconnect is further adapted to selectively engage the power and control system as a result of the trigger coupling or decoupling end.
New embodiments of the present disclosure provide mechanisms for
298 action with integrated status indication, which are capable of providing the incremental state of drug delivery before, during, and after operation of the device, and provide means to ensure compliance with the drug dose, i.e. ensure that has basically delivered the full drug dose to the user. Throughout this specification, unless otherwise indicated, understand, understand, and understand, or related terms or expressions such as include or consist of, are used inclusive rather than exclusive, so that an indicated integer or group of integers may include one or more of other unspecified integers or groups of integers. As will be further described below, embodiments of the present disclosure may include one or more additional components that can be considered conventional components in the mechanical device industry. Components, and embodiments containing such components, are within the contemplation of the present disclosure and are to be understood as falling within the scope and scope of the present disclosure.
Figures 156 and 157A-157B illustrate an embodiment of the action mechanism 3100 including an end of dose indicator 3133. The end of dose indicator 3133 includes a switch interconnect 3132 and a contact sleeve assembly 3120 adapted for movement with the piston. As described above with reference to the embodiments shown in Figures 20A-24B, the piston has an interface surface that is capable of contacting or otherwise supported on the plunger seal to force drug fluid out of the barrel through the fluid path connection to supply a patient. In order to provide access of the end of dose indicator 3133 to the interior of the action housing 3130, the action housing 3130 includes an access window 3131. In at least one embodiment, the action housing 3130 includes more than one access window 3131 to allow passage through more than one switch, sensor, and / or trigger interconnect to, for example, interface with the 3120 mounting of sleeve. In order to better illustrate the relationship between the end of dose indicator 3133 and sleeve assembly 3120 during movement of sleeve assembly 3120, Figures 157A and 157B show housing 3130, sleeve 3126, members 3106, 3122 of fitness, and end-of-dose indicator 3133 in a cross section taken along line 15-15 in Figure 156, before and after actuation, respectively. The 3138 PCB board is included in this view of the 3100 action mechanism to show the interaction between the end of dose indicator 3133 and the 3138 PCB board.
The illustrated end-of-dose indicator 3133 includes a sensor 3134 including a pivotally mounted, essentially mechanical 3135 trigger and a mechanical on / off switch. In at least one embodiment, the end of dose indicator 3133 has
299 more than one trigger 3135 mounted through more than one corresponding window 3131 of the action mechanism 3100, for functional redundancy and / or robustness of operation. Each of the triggers 3135 is disposed in a first position of contact with the sleeve assembly 3120, particularly the sleeve 3126 thereof, when the piston 3110 is in a first retracted position, as illustrated in Figure 157A. When the piston 3110 is moved out of the action housing 3130, the triggers 3135 slide along the telescopic sleeve assembly 3120 until such a time that the proximal end of the second sleeve 3126 passes the windows 3131, i.e. , triggers 3135. When the second sleeve 3126 passes at least one of the triggers 3135, the trigger 3135 moves to a second position, which is illustrated in Figure 157B. Movement of trigger 3135 to the second position results in the transmission of a signal indicating the end of dose in the power and control system. In this configuration, movement of at least one 3135 trigger will cause signal transmission to occur.
One skilled in the art will understand that in some configurations there is the possibility of the arrangement of spring 3122 underlying window 3131 after axial movement of sleeve 3126 can inhibit actuation of sensor 3134 of switch interconnect 3132, for example, by inhibiting movement of trigger 3135 to an actuated position. Although actuation of sensor 3134, or trigger 3135, can only be temporarily avoided, such delay may result in a corresponding delay in indication of end of dose. Therefore, the inclusion of two or more 3134 sensors or 3135 triggers can provide desirable redundancy. In addition, windows 3131 and sensors 3134 can be located to maximize the opportunity for actuation of at least one of triggers 3135 concurrently with the end of the dose delivery. Because more than one trigger 3135 is used in this configuration, the end of dose indicator 3133 provides functional redundancy to ensure that a powered signal is transmitted to the power and control system.
For the purposes of the present disclosure and the appended claims, transmission of a signal means the provision of an indication that end of dose has occurred. That transmission can be associated with a mechanical movement, for example, coupling or decoupling, or an electrical signal, for example, the provision of an electrical signal or connection, or the discontinuation of an electrical signal or connection, or a combination of such transmissions.
In at least one embodiment of the configuration shown in Figures 156-157 B, switch interconnects 3132 are directly coupled to a PCB board 3138 that enables transmission of a signal to the power control system. Switch interconnects 3132 can also be configured to initially connect (for example, a
300 closed or full circuit) or disconnecting (eg, open or broken circuit) from a 3138 PCB board, although the embodiment shown in Figures 157A-157B shows the switch interconnects 3132 initially connected to the 3138 PCB board, is say, before the end of the dose. When the second sleeve 3126 passes at least one of the triggers 3135, as shown in the transition from Figure 157A to Figure 157B, the trigger 3135 moves to a second position, namely, a distance shown as D1 in Figure 157B. Movement of the trigger 3135 to the second position results in, in at least one embodiment, a disconnection of the switch interconnect 3132 from the PCB 3138 and the resulting transmission of a signal indicating the end of dose to the power system and control. Although the illustrated design shows switch interconnect 3132 directly coupled to PCB 3138, it is to be understood that switch interconnect 3132 could alternatively or additionally be coupled to one or more conductive or non-conductive intermediate structures.
The end of dose indicator 3133, triggers 3135, and PCB board 3138 can alternatively be configured, as will be readily understood by one skilled in the art, to cause a connection between them upon movement of trigger 3135 to the second position. By way of example only, a trigger can be switched in such a way that the switch interconnect is not in communication with the PCB prior to the end of dose, with trigger movement at the end of dose causing a connection directly to or transmitted to the PCB board. In addition, as described below, connecting and disconnecting (or vice versa) between switch interconnects 3132 and the PCB can be used to provide incremental status indication.
End of dose indicator 3133 can be of any appropriate design and can be formed from any appropriate material or materials or by any appropriate manufacturing method. The illustrated switch interconnect 3132 may be formed in whole or in part of a conductive material, for example. In an arrangement where electrical connection occurs when trigger 3135 is in the position illustrated in Figure 157A and electrical connection is discontinued when trigger 3135 is in the position illustrated in Figure 157B, for example, at least one Part of the switch interconnect 3132 arranged to engage the PCB 3138 can be formed of or coated with a conductive material. Conversely, in an arrangement where no electrical connection occurs when trigger 3135 is in the position illustrated in Figure 157A and electrical connection occurs when trigger 3135 is in the position illustrated in Figure 157B, for example, at least a portion of switch interconnect 3132 arranged to engage PCB board 3138 may be formed of or coated with an insulating material.
Although it is illustrated as an electromechanical arrangement that reads the position of a
301 With the telescopic cuff, any appropriate arrangement can be provided to read the relative position of any appropriate component, with the end-of-dose indicator providing a signal to the power and control system to indicate that all of the drug has been delivered. In addition, the switch interconnects and corresponding contacts and / or the reference component can be used to provide incremental status indication in addition to an end of dose indication. For example, in the switch interconnect arrangement described above with reference to Figures 20A-24B or Figures 156-157B, the switch interconnect 2132, 3132 may be an electromechanical sensor configured to recognize a variety of protrusions, ridges, or grooves, in the corresponding sleeve 2126, 3126 or any other reference component, the contact with which allows the signal switch interconnection to signal an incremental status indication (eg, start of delivery, number of volumes delivered, duration of plunger stroke, etc.) and an end of dose indication. As described herein, a similar incremental status indication can be provided in this configuration using a different type of sensor arrangement. For example, switch interconnect 2132,3132 may be an optical sensor configured to recognize a variety of markings on corresponding sleeve 2126, 3126, or any other reference component. When the optical sensor recognizes the diversity of markings, it enables the switch interconnect to signal an incremental status indication (eg, start of delivery, quantity of volumes delivered, duration of plunger stroke, etc.) and an end of indication final dose. Any appropriate arrangement for reading the relative position of a variety of respective marks, ridges, grooves, or indicators can be provided on any appropriate reference component, and recognition of such indicators by the switch interconnect enables a signal to be provided to the power system. and monitoring to indicate the incremental state of drug delivery, including the final state that all of the drug has been administered. As the ordinary person skilled in the relevant art will understand, indicators may not necessarily define aspects in a reference component, and switch interconnects can be configured to recognize the actual travel of the reference component itself. Switch interconnects can be configured in this way to recognize the rate of change, travel distance, or other related measurements in the actual travel of components and to allow a signal to the power and control system to provide the user with such information or feedback.
Those skilled in the art will understand that the embodiments of the present disclosure provide the force of action necessary to push a plunger seal and a drug fluid into a drug container, while reducing or minimizing the footprint of the drug.
302 mechanism of action and the device as a whole. Therefore, the present disclosure provides a mechanism of action that can be used in a more compact drug delivery device. The embodiments of the present disclosure can be similarly used to provide additional strength, which may be required for highly viscous drug fluids or for larger volume drug containers.
The embodiments shown and detailed herein disclose only a few possible variations of the present disclosure; Other similar variations are contemplated and incorporated within the scope of the present disclosure.
The mechanism of action may further include one or more contact surfaces located on the corresponding components. Such contact surfaces can be electrical contact surfaces, mechanical contact surfaces, or electromechanical contact surfaces. Such surfaces may initially be in contact and cause them to disengage, or be initially disconnected and cause them to engage, to allow a signal to be sent to and / or from the energy control system 2400.
A fluid path connection, and specifically a sterile sleeve of the fluid path connection, can be connected to the cap and / or pierceable seal of the drug container. A fluid line can be connected to the other end of the fluid path connection that connects itself to the insertion mechanism in such a way that the fluid path, when opened, connected, or otherwise enabled, travels directly from the drug container, the fluid path connection, the fluid passage, the insertion mechanism, and through the cannula for delivery of drug to a user's body. The components that make up the path for fluid flow are now mounted. These components can be sterilized, by a variety of known methods, and then fixedly or removably mounted to a mounting platform or housing of the drug delivery device 10, as shown in Figure 1B.
Certain optional conventional components or variations of the mechanism 100 of action or drug delivery device 10 are contemplated while remaining within the scope and scope of the present disclosure. For example, the upper and lower housings may optionally contain one or more transparent or translucent windows 18, as shown in FIG. 1A, to allow the user to view the operation of the drug delivery device 10 or to verify that the drug dose. In addition, the drug delivery device 10 may contain an adhesive patch 26 and a patch liner 28 on the underside of housing 12. The adhesive patch 26 can be used to adhere the drug delivery device 10 to the user's body for delivery of the drug dose. As will be readily understood by one of ordinary skill in the art, adhesive patch 26 may have an adhesive surface for adhesion of the
303 drug delivery device to the user's body. The adhesive surface of the adhesive patch 26 may initially be covered with a non-adhesive patch liner 28, which is removed from the adhesive patch 26 prior to the placement of the drug delivery device 10 in contact with the user's body. Removal of the patch liner 28 can further remove the sealing membrane 254 from the insertion mechanism 200, opening the insertion mechanism to the user's body for drug delivery (as shown in Figure 1C).
Similarly, one or more of the components of mechanism of action 100 and drug delivery device 10 can be modified while functionally remaining within the scope and scope of the present disclosure. For example, as described above, although the casing of the drug delivery device 10 is shown in the form of two separate components, the upper casing 12A and the lower casing 12B, these components may be a single unified component. Similarly, although electrical contact 134 is shown as a separate component of contact sleeve 140, it may be a unified component printed on the surface of the ring of contact sleeve 140. As discussed above, a glue, adhesive, or other known methods or materials can be used to hold one or more components of the mechanism of action and / or the drug delivery device together. Alternatively, one or more components of the mechanism of action and / or the drug delivery device may be a unified component. For example, the upper casing and the lower casing can be separate components held together by an adhesive or glue, a screw installation connection, an interference installation, fusion bonding, soldering, ultrasonic welding, and the like; or the top shell and bottom shell can be a single unified component. Those of ordinary skill in the art will understand such conventional components and functional variations and are, therefore, within the scope and scope of the present disclosure.
From the foregoing description, it is to be understood that the mechanisms of action and drug delivery devices disclosed herein provide an efficient and easily operated system for automated drug delivery from a drug container. The new embodiments described herein provide an integrated status indication to provide feedback to the user. The new mechanisms of action of the present disclosure can be activated directly or indirectly by the user. For example, in at least one embodiment the locking bolt or bolts that hold the actuating mechanism in its energized, locked state are moved directly from the corresponding locking grooves of the piston 110 by user actuation of the actuating mechanism. Furthermore, the
304 New configurations of the mechanism of action and drug delivery devices of the present disclosure maintain the sterility of the fluid path during storage, transport, and in operation of the device. Because the path the drug fluid travels within the device is fully maintained in sterile conditions, only these components need to be sterilized during the manufacturing process. Such components include the drug container of the mechanism of action, the fluid path connection, the sterile fluid passage, and the insertion mechanism. In at least one embodiment of the present disclosure, the power and control system, mounting platform, control arm, trigger mechanism, housing, and other components of the drug delivery device do not need to be sterilized. This greatly improves the manufacturing capacity of the device and reduces associated mounting costs. Therefore, the devices of the present disclosure do not require terminal sterilization upon completion of assembly. An additional benefit of the present disclosure is that the components described herein are designed to be modular in such a way that, for example, the housing and other components of the drug delivery device can be easily configured to accept and operating the mechanism of action 100, the mechanism 500 of action, or a variety of other variations of the mechanism of action described herein.
Manufacture of a drug delivery device includes the step of attaching the mechanism of action and the drug container, either separately or in the form of a combined component, to a mounting platform or housing of the drug delivery device. The manufacturing method further includes attaching the fluid path connection, the drug container, and the insertion mechanism to the mounting platform or housing. Additional components of the drug delivery device, as described above, including the power and control system, the trigger mechanism, and the control arm can be attached, pre-formed, or pre-mounted to the mounting platform or housing . An adhesive patch and a patch liner can be attached to the housing surface of the drug delivery device that contacts the user during operation of the device.
A method of operating the drug delivery device includes the steps of: activating, by a user, the activation mechanism; move a control arm to operate an insertion mechanism; and actuating a power and control system to activate an action control mechanism to direct the flow of fluid drug through the drug delivery device. The method may further include the step of: attaching a sensor to the optional body prior to activation of the trigger mechanism. The method may similarly include the step of: establishing a connection between a fluid path connection and a
305 drug container. In addition, the method of operation may include moving a plunger seal within the action control mechanism and the drug container to force fluid drug flow through the drug container, the fluid path connection, a fluid line. sterile, and the insertion mechanism for delivery of the fluid drug to the user's body. The method of operation of the insertion mechanism and the drug delivery device can be better understood by referring to Figures 14A-14E, which have been described above.
XXIV. Drug information
The foregoing description describes various systems and methods for the use of various drug delivery devices. It should be clear that drug delivery systems, devices, or methods may further comprise the use of a drug listed below with the caveat that the following list should not be considered to be all inclusive or limiting. The medicament is contained in a reservoir (eg, container 50, container 618, container 718, container 818, container 918, container 1118, container 2050, container 6050, container 8050). In some cases, the reservoir is a primary container that is filled or pre-filled for treatment with the medication. The primary container can be a cartridge or a pre-filled syringe. Also, in some cases, the reservoir may be a primary container that is pre-loaded.
For example, the drug delivery device or more specifically the device reservoir can be filled with colony stimulating factors, such as granulocyte colony stimulating factor (G-CSF). Such G-CSF agents include, but are not limited to, Neupogen® (filgrastim) and Neulasta® (pegfilgrastim). In various other embodiments, the drug delivery device can be used with various pharmaceuticals, such as an erythropoiesis stimulating agent (ESA), which can be in liquid or lyophilized form. An ESA is any molecule that stimulates erythropoiesis, such as Epogen® (epoetin alfa), Aranesp® (darbepoetin alfa), Dynepo® (epoetin delta), Mircera® (methoxy polyethylene glycol-epoetin beta), Hematide®, MRK-2578, INS-22, Retacrit® (epoetin zeta), Neorecormon® (epoetin beta), Silapo® (epoetin zeta), Binocrit® (epoetin alfa), epoetin alfa Hexal, Abseamed® (epoetin alfa), Ratioepo® (epoetin theta), Eporatio® (epoetin theta), Biopoin® (epoetin theta), epoetin alfa, epoetin beta, epoetin zeta, epoetin theta, and epoetin delta, as well as the molecules or variants or analogs thereof disclosed in the following patent documents or patent applications, each of which is incorporated herein by reference in its entirety: US Patent documents numbered 4,703,008; 5,441,868; 5,547,933; 5,618,698; 5,621,080; 5,756,349; 5,767,078; 5,773,569; 5,955,422; 5,986,047; 6,583,272; 7,084,245; and 7,271,689; and PCT Publication documents with numbers WO 91/05867; WO 95/05465;
306
WO 96/40772; WO 00/24893; WO 01/81405; and WO 2007/136752.
An ESA can be an erltropoiesis stimulating protein. As used herein, erythropoiesis stimulating protein means any protein that directly or indirectly causes erythropoietin receptor activation, for example, by binding to or causing receptor dimerization. Erythropoiesis-stimulating proteins include erythropoietin and variants, analogs, or derivatives thereof that bind to and activate the erythropoietin receptor; antibodies that bind to the erythropoietin receptor and activate the receptor; or peptides that bind to and activate the erythropoietin receptor. Some erythropoiesis-stimulating proteins include, but are not limited to, epoetin alfa, epoetin beta, epoetin delta, epoetin omega, epoetin iota, epoetin zeta, and analogs thereof, erythropoietin pegylated, carbamylated erythropoietin, mlmetic peptides (including EMP1 / hematide), and mimetic antibodies. Some exemplary erythropoiesis-stimulating proteins include erythropoietin, darbepoetin, erythropoietin agonist variants, and peptides or antibodies that bind and activate the erythropoietin receptor (and include compounds that are reported in the United States Publication docs. with numbers 2003/0215444 and 2006/0040858, the disclosures of each of which are incorporated herein by reference in their entirety) as well as the erythropoietin molecules or variants or analogs thereof disclosed in the following patent or patent application documents, which Each is incorporated herein by reference in its entirety: US Patent documents numbers 4,703,008; 5,441,868; 5,547,933; 5,618,698; 5,621,080; 5,756,349; 5,767,078; 5,773,569; 5,955,422; 5,830,851; 5,856,298; 5,986,047; 6,030,086; 6,310,078; 6,391,633; 6,583,272; 6,586,398; 6,900,292; 6,750,369; 7,030,226; 7,084,245; and 7,217,689; United States Publication documents under numbers 2002/0155998; 2003/0077753; 2003/0082749; 2003/0143202; 2004/0009902; 2004/0071694; 2004/0091961; 2004/0143857; 2004/0157293; 2004/0175379; 2004/0175824; 2004/0229318; 2004/0248815; 2004/0266690; 2005/0019914; 2005/0026834; 2005/0096461; 2005/0107297; 2005/0107591; 2005/0124045; 2005/0124564; 2005/0137329; 2005/0142642; 2005/0143292; 2005/0153879; 2005/0158822; 2005/0158832; 2005/0170457; 2005/0181359; 2005/0181482; 2005/0192211; 2005/0202538; 2005/0227289; 2005/0244409; 2006/0088906; and 2006/0111279; and PCT Publication documents with numbers WO 91/05867; WO 95/05465; WO 99/66054; WO 00/24893; WO 01/81405; WO 00/61637; WO 01/36489; WO 02/014356; WO 02/19963; WO 02/20034; WO 02/49673; WO 02/085940; WO 03/029291; WO 2003/055526; WO 2003/084477; WO 2003/094858; WO 2004/002417; WO 2004/002424; WO 2004/009627; WO 2004/024761; WO 2004/033651; WO 2004/035603; WO 2004/043382; WO 2004/101600; WO 2004/101606; WO 2004/101611; WO 2004/106373; WO 2004/018667; WO 2005/001025; WO 2005/001136; WO
307
2005/021579; WO 2005/025606; WO 2005/032460; WO 2005/051327; WO 2005/063808; WO 2005/063809; WO 2005/070451; WO 2005/081687; WO 2005/084711; WO 2005/103076; WO 2005/100403; WO 2005/092369; WO 2006/50959; WO 2006/02646; and WO 2006/29094.
Some examples of other pharmaceuticals for use with the device may include, but are not limited to, antibodies such as Vectibix® (panitumumab), Xgeva ™ (denosumab), and Prolia ™ (denosamab); other biological agents such as Enbrel® (etanercept, TNF / Fc receptor fusion protein, TNF blocker), Neulasta® (pegfilgrastim, pegylated filgastrim, pegylated G-CSF, pegylated hu-Met-G-CSF), Neupogen® (filgrastim, G-CSF, hu-MetG-CSF), and Nplate® (romiplostim); small molecule drugs such as Sensipar® (cinacalcet). The device can also be used with a therapeutic antibody, polypeptide, protein, or other chemical compound, such as an iron, for example, ferumoxytol, iron dextrans, ferric glyconate, and iron sucrose. The pharmaceutical product can be in liquid form, or reconstituted from a lyophilized form.
Particular illustrative proteins include the specific proteins discussed below, including fusions, fragments, analogs, variants, or derivatives thereof:
OPGL-specific antibodies, peptibodies, and related proteins, and the like (also called RANKL-specific antibodies, peptibodies, and the like), including fully humanized and human OPGL-specific antibodies, particularly fully humanized monoclonal antibodies, including, but not are limited to, the antibodies described in PCT Publication Document No. WO 03/002713, which is incorporated herein in its entirety with respect to specific antibodies against OPGL and antibody-related proteins, particularly those having the sequences set forth therein, particularly, but not limited to, those set forth in same: 9H7; 18B2; 2D8; 2E11; 16E1; and 22B3, including OPGL-specific antibodies having the SEQ ID NO: 2 light chain set forth therein in Figure 2 and / or the SEQ ID NO: 4 heavy chain set forth therein. in Figure 4, each of which is incorporated individually and specifically by reference herein in its entirety in its entirety as disclosed in the previous publication;
Myostatin-binding proteins, peptibodies, and related proteins, and the like, including myostatin-specific peptibodies, particularly those described in US Publication Document No. 2004/0181033 and PCT Publication Document No. WO 2004/058988, which are incorporated by reference herein in their entirety, particularly in the relevant parts to myostatin-specific peptibodies, including, but not limited to, the peptibodies of the family
308 mTN8-19, including those in SEQ ID NOS: 305-351, including TN8-19-1 to TN8-19-40, TN8-19 con1 and TN8-19 con2; the mL2 family peptibodies from SEQ ID NOS: 357-383; the ml_15 family of SEQ ID NOS: 384-409; the mL17 family of SEQ ID NOS: 410-438; the mL20 family of SEQ ID NOS: 439-446; the mL21 family of SEQ ID NOS: 447-452; the mL24 family of SEQ ID NOS: 453-454; and those of SEQ ID NOS: 615-631, each of which is incorporated individually and specifically by reference herein in its entirety in its entirety as disclosed in the previous publication;
Specific antibodies to the IL-4 receptor, peptibodies, and related proteins, and the like, particularly those that inhibit activities mediated by binding of IL-4 and / or IL-13 to the receptor, including those described in PCT Publication Document No. WO 2005/047331 or PCT Application Document No. PCT / US2004 / 37242 and in United States Publication Document No. 2005/112694, which are incorporated herein by reference in their entirety particularly in the pertinent parts to specific antibodies against the IL-4 receptor, particularly antibodies such as those described therein, particularly, and without limitation, those which are denominate in them: L1H1; L1H2; L1H3; L1H4; L1H5; L1H6; L1H7; L1H8; L1H9; L1H10; L1H11; L2H1; L2H2; L2H3; L2H4; L2H5; L2H6; L2H7; L2H8; L2H9; L2H10; L2H11; L2H12; L2H13; L2H14; L3H1; L4H1; L5H1; L6H1, each of which is incorporated individually and specifically by reference herein in its entirety in its entirety as disclosed in the previous publication;
Specific antibodies to interleukin 1 receptor 1 ("IL1-R1"), peptibodies, and related proteins, and the like, including, but not limited to, those described in US Publication Document No. 2004/097712, which is incorporated herein by reference in its entirety in parts relevant to IL1-R1 specific binding proteins, in particular monoclonal antibodies, especially, without limitation, those referred to therein: 15CA, 26F5, 27F2, 24E12, and 10H7, each of which is incorporated individually and specifically by reference herein in its entirety in its entirety as disclosed in the aforementioned publication;
Ang2-specific antibodies, peptibodies, and related proteins, and the like, including, but not limited to, those described in PCT Publication Document No. WO 03/057134 and United States Publication Document No. No. 2003/0229023, each of which is incorporated herein by reference in its entirety particularly in parts relevant to specific Ang2 antibodies and peptibodies, and the like, especially those of the sequences described therein and including, but not limited to: L1 (N); L1 (N) WT; L1 (N) 1K WT; 2xL1 (N); 2xL1 (N) WT; Con4 (N), Con4 (N) 1K WT, 2xCon4 (N) 1K; L1C; L1C 1K; 2xL1C; Con4C; Con4C
309
1Κ; 2xCon4C 1Κ; Con4-L1 (N); Con4-L1C; TN-12-9 (N); C17 (N); TN8-8 (N); TN8-14 (N); With 1 (N), also including anti-Ang 2 antibodies and formulations such as those described in PCT Publication Document No. WO 2003/030833 which is incorporated herein by reference in its entirety as to the same , particularly Ab526; Ab528; Ab531; Ab533; Ab535; Ab536; Ab537; Ab540; Ab543; Ab544; Ab545; Ab546; A551; Ab553; Ab555; Ab558; Ab559; Ab565; AbFlAbFD; AbFE; AbFJ; AbFK; AbG1D4; AbGC1E8; AbH1C12; AblA1; AbIF; AbIK, AblP; and AblP, in their various permutations as described therein, each of which is incorporated individually and specifically by reference herein in its entirety in its entirety as disclosed in the previous publication;
Specific antibodies to NGF, peptibodies, and related proteins, and the like including, in particular, but not limited to, those described in United States Publication Document No. 2005/0074821 and United States Patent Document No. 6,919,426, which are incorporated herein by reference in their entirety particularly with regard to specific antibodies to NGF and related proteins, including, in particular, but are not limited to, specific antibodies to NGF referred to herein as 4D4, 4G6, 6H9, 7H2, 14D10 and 14D11, each of which is incorporated individually and specifically by reference herein in its entirety in its entirety as disclosed in the previous publication;
CD22-specific antibodies, peptibodies, and related proteins, and the like, such as those described in US Patent No. 5,789,554, which are incorporated herein by reference in their entirety in which refers to specific antibodies against CD22 and related proteins, particularly specific antibodies against human CD22, such as, but not limited to, humanized and fully human antibodies, including, but not limited to, humanized and fully human monoclonal antibodies, including, but not limited to, specific IgG antibodies to human CD22, such as, for example, a dimer of a hLL2 gamma chain of antibody human-mouse monoclonal disulfide-bridged to a human-mouse monoclonal antibody hLL2 kappa chain, including, but not limited to, for example, the fully humanized antibody specific against human CD22 in Epratuzumab, CAS registry number 501423-23-0;
IGF-1 receptor specific antibodies, peptibodies, and related proteins, and the like, such as those described in PCT Publication Document No. WO 06/069202, which is incorporated herein by reference in its all in terms of specific antibodies against the IGF-1 receptor and related proteins, including, but not limited to, specific antibodies against IGF-1 called L1H1, L2H2, L3H3, L4H4, L5H5, L6H6, L7H7, L8H8, L9H9, LT0H10, L11H11, L12H12,
310
L13H13, L14H14, L15H15, L16H16, L17H17, L18H18, L19H19, L20H20, L21H21, L22H22,
L23H23, L24H24, L25H25, L26H26, L27H27, L28H28, L29H29, L30H30, L31H31, L32H32,
L33H33, L34H34, L35H35, L36H36, L37H37, L38H38, L39H39, L40H40, L41H41, L42H42,
L43H43, L44H44, L45H45, L46H46, L47H47, L48H48, L49H49, L50H50, L51H51, L52H52, and IGF-1R binding fragments and derivatives thereof, each of which is incorporated individually and specifically by reference herein entirely in its entirety as disclosed in the previous publication;
Furthermore, non-limiting examples of anti-IGF-1R antibodies for use in the methods and compositions of the present disclosure include each and every one described in:
(i) United States Publication documents numbered 2006/0040358 (published on February 23, 2006), 2005/0008642 (published on January 13, 2005), 2004/0228859 (published on November 18, 2004) , which include, but are not limited to, for example, antibody 1A (Deposit # DSMZ DSM ACO 2586), antibody 8 (Deposit # DSMZ DSM ACC 2589), antibody 23 (DSMZ No. Deposit No. DSMZ DSM ACC 2588) and the antibody 18 described therein;
(¡I) PCT Publication documents No. WO 06/138729 (published on December 28, 2006) and WO 05/016970 (published on February 24, 2005), and Lu etal. (2004), J. Biol. Chem. 279: 2856-2865, which include, but are not limited to, the 2F8, A12, and IMC-A12 antibodies described therein;
(¡Ii) PCT Publication documents No. WO 07/012614 (published on February 1, 2007), WO 07/000328 (published on January 4, 2007), WO 06/013472 (published on February 9 2006), WO 05/058967 (published June 30, 2005), and WO 03/059951 (published July 24, 2003);
(iv) United States Publication Document No. 2005/0084906 (published April 21, 2005), which includes, but is not limited to, the 7C10 antibody, the C7C10 chimeric antibody, the h7C10 antibody, the antibody 7H2M, the chimeric antibody * 7C10, the GM 607 antibody, the humanized antibody 7C10 version 1, the humanized antibody 7C10 version 2, the humanized antibody 7C10 version 3, and the 7H2HM antibody, described therein;
(v) United States Publication documents with numbers 2005/0249728 (published on November 10, 2005), 2005/0186203 (published on August 25, 2005), 2004/0265307 (published on December 30, 2004) , and 2003/0235582 (published December 25, 2003) and Maloney et al. (2003), Cancer Res. 63: 5073-5083, including, but not limited to, antibody EM164, resurfaced EM164, humanized EM164, huEM164 v1.0, huEM164 v1.1, huEM164 v1.2, and huEM164 v1.3 described in themselves;
311 (vi) United States Patent Document No. 7,037,498 (published on May 2, 2006), United States Publication documents with numbers 2005/0244408 (published on November 30, 2005) and 2004 / 0086503 (published on May 6, 2004), and Cohén, et al. (2005), Clinical Cancer Res. 11: 2063-2073, for example, the CP751.871 antibody, which include, but are not limited to, each of the antibodies produced by hybridomas that have ATCC registration numbers PTA-2792, PTA-2788, PTA -2790, PTA2791, PTA-2789, PTA-2793, and antibodies 2.12.1,2.13.2, 2.14.3, 3.1.1,4.9.2, and 4.17.3, which are described therein;
(vii) United States Publication documents numbered 2005/0136063 (published June 23, 2005) and 2004/0018191 (published January 29, 2004), which include, but are not limited to, the 19D12 antibody and an antibody comprising a polynucleotide encoded heavy chain on plasmid 15H12 / 19D12 HCA (y4), deposited with the ATCC under the number PTA-5214, and a polynucleotide encoded light chain on plasmid 15H12 / 19D12 LCF ( k), deposited with the ATCC under the number PTA-5220, which are described therein; and (viii) US Publication Document No. 2004/0202655 (published October 14, 2004), which includes, but is not limited to, the antibodies PINT-6A1, PINT-7A2, PINT-7A4, PINT-7A5, PINT-7A6, PINT-8A1, PINT-9A2, PINT-11A1, PINT-11A2, PINT-11A3, PINT-11A4, PINT-11A5, PINT-11A7, PINT-11A12, PINT-12A1, PINT- 12A2, PINT-12A3, PINT12A4, and PINT-12A5, which are described therein; each and every one of which is incorporated herein by reference in its entirety, particularly as it relates to the aforementioned antibodies, peptibodies, and related proteins and the like that target IGF-1 receptors;
Antibodies specific against B-7 related protein 1, peptibodies, related proteins and the like ("B7RP-1", also referred to in the literature as B7H2, ICOSL, B7h, and CD275), particularly B7RP specific fully human monoclonal lgG2 antibodies , particularly fully human lgG2 monoclonal antibody that binds to an epitope in the first immunoglobulin-like domain of B7RP-1, especially those that inhibit the interaction of B7RP-1 with its natural receptor, ICOS, particularly in activated T lymphocytes, especially, in all that is indicated above, those disclosed in the document of United States Publication n. No. 2008/0166352 and PCT Publication Document No. WO 07/011941, which are incorporated herein by reference in their entirety as regards such antibodies and related proteins, including, but not limited to, the antibodies named therein as follows: 16H (having the variable light chain and heavy chain variable SEQ ID NO: 1 and SEQ ID NO: 7, respectively, therein);
312
5D (having the variable light chain and heavy chain variable SEQ ID NO: 2 and SEQ ID NO: 9, respectively, therein); 2H (having the variable light chain and heavy chain variable SEQ ID NO: 3 and SEQ ID NO: 10, respectively, therein); 43H (having the variable light chain and heavy chain variable SEQ ID NO: 6 and SEQ ID NO: 14, respectively, therein); 41H (having the variable light chain and heavy chain variable SEQ ID NO: 5 and SEQ ID NO: 13, respectively, therein); and 15H (having the variable light chain and heavy chain variable SEQ ID NO: 4 and SEQ ID NO: 12, respectively, therein), each of which is incorporated individually and specifically by reference herein. document in its entirety completely as disclosed in previous publications;
Specific antibodies to IL-15, peptibodies, and related proteins, and the like, such as, in particular, humanized monoclonal antibodies, particularly antibodies such as those disclosed in US Publication Documents No. 2003/0138421; 2003/023586; and 2004/0071702; and US Patent No. 7,153,507, each of which is incorporated herein by reference in its entirety with respect to specific antibodies to IL-15 and related proteins, including peptibodies, particularly including, for example, but not limited to, HuMax IL-15 antibodies and related proteins, such as, for example, 146B7;
Specific antibodies to IFN, peptibodies, and related proteins and the like, especially antibodies specific to human IFN gamma, particularly specific anti-fully human IFN antibodies, such as, for example, those described in US Publication Document No. 2005/0004353, which is incorporated herein by reference in its entirety with respect to specific antibodies against IFN gamma, particularly, for example, antibodies named therein 1118; 1118 *; 1119; 1121; and 1121 *. The complete heavy and light chain sequences of each of these antibodies, as well as the sequences of the heavy and light chain variable regions and the complementarity determining regions, are each incorporated individually and specifically by reference herein in entirely in their entirety as disclosed in the previous publication and in Thakur et al. (1999), Mol. Immunol. 36: 1107-1115. Furthermore, the description of the properties of these antibodies provided in the previous publication is also incorporated by reference herein in its entirety. Specific antibodies include those having the heavy chain of SEQ ID NO: 17 and the light chain of SEQ ID NO: 18; those having the heavy chain variable region of SEQ ID NO: 6 and the light chain variable region of SEQ ID NO: 8; those with the heavy chain of SEQ ID NO: 19 and the light chain
313 SEQ ID NO: 20; those having the heavy chain variable region of SEQ ID NO: 10 and the light chain variable region of SEQ ID NO: 12; those having the heavy chain of SEQ ID NO: 32 and the light chain of SEQ ID NO: 20; those having the heavy chain variable region of SEQ ID NO: 30 and the light chain variable region of SEQ ID NO: 12; those having the heavy chain sequence of SEQ ID NO: 21 and the light chain sequence of SEQ ID NO: 22; those having the heavy chain variable region of SEQ ID NO: 14 and the light chain variable region of SEQ ID NO: 16; those with the heavy chain of SEQ ID NO: 21 and the light chain of SEQ ID NO: 33; and those having the heavy chain variable region of SEQ ID NO: 14 and the light chain variable region of SEQ ID NO: 31, which are disclosed in the previous publication. A specific antibody contemplated is antibody 1119 which is disclosed in the above US publication document and which has a complete heavy chain of SEQ ID NO: 17 as disclosed therein and which has a complete light chain of SEQ ID NO : 18 as disclosed therein;
TALL-1 specific antibodies, peptibodies and related proteins, and the like, and other TALL specific binding proteins, such as those described in US Publication Nos. 2003/0195156 and 2006/0135431, each of which is incorporated herein by reference in its entirety as it relates to TALL-1 binding proteins, particularly the molecules in Tables 4 and 5B, each of which is incorporated individually and specifically by reference herein in its entirety in its entirety as disclosed in the foregoing publications;
Specific antibodies against parathyroid hormone ("PTH"), peptibodies, and related proteins, and the like, such as those described in US Patent No. 6,756,480, which is incorporated herein by reference in its entirety, particularly in the parts relevant to the proteins that bind to PTH;
Thrombopoietin receptor-specific antibodies ("TPO-R"), peptibodies, and related proteins, and the like, such as those described in US Patent No. 6,835,809, which is incorporated in this document by reference in its entirety, particularly in the relevant parts to the proteins that bind to TPO-R;
Specific hepatocyte growth factor ("HGF") antibodies, peptibodies, and related proteins, and the like, including those that target the HGF / SF: cMet axis (HGF / SF: c-Met), such as the fully human monoclonal antibodies that neutralize scattered factor / hepatocyte growth factor (HGF / SF) that are described in US Publication Document No. 2005/0118643 and PCT Publication Document No. WO 2005 / 017107, huL2G7 described in the document
314
United States Patent No. 7,220,410 and OA-5d5 described in United States Patent Documents Nos. 5,686,292 and 6,468,529 and in PCT Publication Document No. WO 96/38557, each of which is incorporated herein by reference in its entirety, particularly in the relevant parts to proteins that bind to HGF;
Specific antibodies to TRAIL-R2, peptibodies, related proteins, and the like, such as those described in US Patent No. 7,521,048, which is incorporated herein by reference in its entirety, particularly in the parts relevant to the proteins that bind TRAIL-R2;
Activin A-specific antibodies, peptibodies, related proteins, and the like, including, but not limited to, those described in US Publication Document No. 2009/0234106, which is incorporated herein by reference in its entirety, particularly in the parts relevant to the proteins that bind to Activin A;
TGF-beta specific antibodies, peptibodies, related proteins, and the like, including, but not limited to, those described in US Patent No. 6,803,453 and US Publication Document United No. 2007/0110747, each of which is incorporated herein by reference in its entirety, particularly in parts relevant to proteins that bind TGFbeta;
Specific antibodies to beta-amyloid protein, peptibodies, related proteins, and the like, including, but not limited to, those described in PCT Publication Document No. WO 2006/081171, which is incorporated in this document by reference in its entirety, particularly in the parts relevant to proteins that bind to beta-amyloid proteins. A contemplated antibody is an antibody having a heavy chain variable region comprising SEQ ID NO: 8 and a light chain variable region having SEQ ID NO: 6 which is disclosed in the previous publication;
C-Kit specific antibodies, peptibodies, related proteins, and the like, including, but not limited to, those described in US Publication Document No. 2007/0253951, which is incorporated herein document by reference in its entirety, particularly in parts relevant to c-Kit binding proteins and / or other stem cell factor receptors;
Specific antibodies to OX40L, peptibodies, related proteins, and the like, including, but not limited to, those described in US Publication Document No. 2006/0002929, which is incorporated herein by Reference in its entirety, particularly in the pertinent parts to proteins that bind to OX40L and / or other 0X40 receptor ligands; and
315
Other exemplary proteins, including Activase® (alteplase, tPA); Aranesp® (darbepoetin alfa); Epogen® (epoetin alfa, or erythropoietin); GLP-1, Avonex® (interferon betala); Bexxar® (tositumomab, anti-CD22 monoclonal antibody); Betaseron® (interferon-beta); Campath® (alemtuzumab, anti-CD52 monoclonal antibody); Dynepo® (epoetin delta); Velcade® (bortezomib); MLN0002 (anti-a4B7 mAb); MLN1202 (mAb vs. anti-CCR2 chemokine receptor); Enbrel® (etanercept, TNF / Fc receptor fusion protein, TNF blocker); Eprex® (epoetin alfa); Erbitux® (cetuximab, anti-EGFR / HER1 / c-ErbB1); Genotropin® (somatropin, human growth hormone); Herceptin® (trastuzumab, anti-HER2 / neu receptor (erbB2) mAb); Humatrope® (somatropin, human growth hormone); Humira® (adalimumab); insulin in solution; Infergen® (interferon alfacon-1); Natrecor® (nesiritide; recombinant human type B natriuretic peptide (hBNP); Kineret® (anakinra); Léukine® (sargamostim, rhuGM-CSF); LymphoCide® (epratuzumab, antiCD22 mAb); Benlysta ™ (linfostat B, belimumab, anti-BlyS mAb); Metalyse® (tenecteplase, t-PA analog); Mircera® (methoxy polyethylene glycol-epoetin beta); Mylotarg® (gemtuzumab ozogamicin); Raptiva® (efalizumab); Cimzia® (certolizumab pegol, CDP 870); Soliris ™ (eculizumab); pexelizumab (anti-C5 complement); Numax® (MEDI-524); Lucentis® (ranibizumab); Panorex® (17-1A, edrecolomab); Trabio® (lerdelimumab); TheraCim hR3 (nimotuzumab); Omnitarg (pertuzumab, 2C4); Osidem® (IDM-1); OvaRex® (B43.13); Nuvion® (visilizumab); cantuzumab mertansine (huC242-DM1); NeoRecormon® (epoetin beta); Neumega® (oprelvechin, interleukin-11 human); Neulasta® (pegylated filgastrim, profiled pegylated G-CSF, pegylated hu-Met-G-CSF); Neupogen® (filgrastim, G-CSF, hu-MetG-CSF); Orthoclone OKT3® (muromonab-CD3, anti-CD3 monoclonal antibody); Procrit® (epoetin alfa); Remicade® (infliximab, anti-TNFa monoclonal antibody); Reopro® (abciximab, anti-GP llb / llia receptor monoclonal antibody); Actemra® (mAb Receptor anti-IL6); Avastin® (bevacizumab), HuMax-CD4 (zanolimumab); Rituxan® (rituximab, anti-CD20 mAb); Tarceva® (erlotinib); Roferon-A®- (interferon alfa-2a); Simulect® (basiliximab); Prexige® (lumiracoxib); Synagis® (palivizumab); 146B7-CHO (anti-IL15 antibody, see US Patent No. 7,153,507); Tysabri® (natalizumab, anti-integrin a4 mAb); Valortim® (MDX-1303, mAb against anti-B protective antigen. anthracis); ABthrax ™; Vectibix® (panitumumab); Xolair® (omalizumab); ETI211 (anti-MRSA mAb); IL-1 trap (the human Fe lgG1 part and the extracellular domains of both components of the IL-1 receptor (the Type I receptor and the receptor accessory protein)); VEGF trap (Ig domains of VEGFR1 fused with Fe of IgG1); Zenapax® (daclizumab); Zenapax® (daclizumab, anti-IL2Ra mAb); Zevalin® (ibritumomab tiuxetano); Zetia® (ezetimibe); Orencia® (atacicept, TACI-lg); anti-CD80 monoclonal antibody (galiximab); anti-CD23 mAb (lumiliximab); BR2-Fc (huBR3 / huFc fusion protein, soluble BAFF antagonist); CNTO 148 (golimumab, anti mAb
316
TNFa); HGS-ETR1 (mapatumumab; human anti-TRAIL Receptor-1 mAb); HuMax-CD20 (ocrelizumab, anti-human CD20 mAb); HuMax-EGFR (zalutumumab); M200 (volociximab, anti-integrin α5β1 mAb); MDX-010 (ipilimumab, anti-CTLA-4 and VEGFR-1 mAb (IMC-18F1); antiBR3 mAb; mAbs against Toxin A and Anti-C Toxin B. difficile C MDX-066 (CDA-1) and MDX-1388); dsFv anti-CD22-PE38 conjugates (CAT-3888 and CAT-8015); anti-CD25 mAb (HuMax-TAC); anti-CD3 mAb (NI-0401); adecatumumab; anti-CD30 mAb (MDX-060); MDX-1333 (anti-IFNAR); anti-CD38 mAb (HuMax CD38); anti-CD40L mAb; anti-Crypto mAb; Idiopathic Pulmonary Fibrosis Phase 1 Fibrinogen anti-CTGF (FG-3019); anti-CTLA4 mAb; anti-eotaxin1 mAb (CAT-213); anti-FGF8 mAb; GD2 anti-ganglioside mAb; GM2 anti-ganglioside mAb; anti-GDF8 human mAb (MYO-029); antl-GM-CSF Receptor mAb (CAM-3001); anti-HepC mAb (HuMax HepC); anti-IFNa mAb (MEDI-545, MDX-1103); anti-IGF1R mAb; anti-IGF-1R mAb (HuMax-Inflam); anti-IL12 mAb (ABT-874); anti-IL12 / IL23 mAb (CNTO 1275); anti-IL13 mAb (CAT-354); antiIL2Ra mAb (HuMax-TAC); anti-IL5 Receptor mAb; anti-integrin receptor mAbs (MDX-018, CNTO 95); Anti-Ulcerative Colitis mAb IP10 (MDX-1100); anti-LLY antibody; BMS-66513; anti-Mannose Receptor / hCGp mAb (MDX-1307); dsFv anti-mesothelin-PE38 conjugate (CAT5001); anti-PD1 mAb (MDX-1106 (ONO-4538)); anti-PDGFRa antibody (IMC-3G3); antiTGFB mAb (GC-1008); TRAIL anti-Receptor-2 human mAb (HGS-ETR2); anti-TWEAK mAb; anti-VEGFR / Flt-1 mAb; anti-ZP3 mAb (HuMax-ZP3); antibody No. 1 NVS; and antibody # 2 NVS.
An antibody to sclerostin may also be included, such as, but not limited to, romosozumab, blosozumab, or BPS 804 (Novartis). Therapeutic substances such as rilotumumab, bixalomer, trebananib, ganitumab, conatumumab, motesanib diphosphate, brodalumab, vidupiprant, panitumumab, denosumab, NPLATE, PROLIA, VECTIBIX or XGEVA may also be included. In addition, a monoclonal antibody (IgG) that binds to Human Subtilisin Proprotein / Kexin Convertase Type 9 (PCSK9) can be included in the device. Such specific antibodies against PCSK9 include, but are not limited to, Repatha® (evolocumab) and Praluent® (alirocumab), as well as molecules, variants, analogs and derivatives thereof which are disclosed in the following patent or application documents of patent, each of which is incorporated herein by reference in its entirety for all purposes: United States Patent No. 8,030,547, United States Patent No. 8,563,698, United States Patent No. 8,829,165, United States Patent No. 8,859,741, United States Patent No. 8,871,913, United States Patent No. 8,871,914, United States Patent No. 8,883,983, United States Patent No. 8,889,834, United States Patent No. 8,981,064, Patent U.S. Patent No. 9,056,915, U.S. Patent No. 8,168,762, U.S. Patent No. 9,045,547, United States Patent No. 8,030,457, United States Patent No. 8,030,457, United States Patent No. 8,829,165,
317
United States Patent No. 8,981,064, United States Patent No. 8,030,457, United States Publication Document No. 2013/0064825, United States Patent Application Publication No. 2012/0093818 , United States Patent Application Publication No. 2013/0079502, United States Patent Application Publication No. 2014/0357850, United States Patent Application Publication No. 2011/0027287, United States Patent Application Publication No. 2014/0357851, United States Patent Application Publication No. 2014/0357854, United States Patent Application Publication No. 2015/0031870, Patent Application Publication United States Patent No. 2013/0085265, United States Patent Application Publication No. 2013/0079501, United States Patent Application Publication No. 2012/0213797, United States Patent Application Publication No. 2012/0251544, United States Patent Application Publication No. 2013/0072665, United States Patent Application Publication No. 2013/0058944, Patent Application Publication United States Patent No. 2013/0052201, United States Patent Application Publication No. 2012/0027765, United States Patent Application Publication No. 2015/0087819, United States Patent Application Publication No. 2011/0117011, United States Patent Application Publication No. 2015/0004174, United States Provisional Patent Application No. 60 / 957,668, United States Provisional Patent Application United States No. 61 / 008,965, United States Provisional Patent Application No. 61 / 010,630, United States Provisional Patent Application No. 61 / 086,133, United States Provisional Patent Application No. 61 / 125,304, United States Provisional Patent Application No. 61 / 798,970, United States Provisional Patent Application No. 61 / 841,039, United States Provisional Patent Application No. 62 / 002,623, United States Provisional Patent Application No. # 62 / 024,399, United States Provisional Patent Application No. 62 / 019,729, United States Provisional Patent Application No. 62 / 067,637, United States Patent Application No. 14 / 777,371, International Patent Application No. PCT / US2013 / 048714, International Patent Application No. PCT / US2015 / 040211, International Patent Application No. PCT / US2015 / 056972, International Patent Application Publication No. WO / 2008/057457, International Patent Application Publication No. WO / 2008/057458, International Patent Application Publication No. WO / 2008/057459, International Patent Application Publication No. WO / 2008/063382, International Patent Application Publication No. WO / 2008/133647, International Patent Application Publication No. WO / 2009/100297, International Patent Application Publication No. WO / 2009/100318, Patent Application Publication International No. WO / 2011/037791, International Patent Application Publication No. WO / 2011/053759, International Patent Application Publication No. WO / 2011/053783, International Patent Application Publication No. WO / 2008/125623, International Patent Application Publication No. WO / 2011/072263,
318
International Patent Application Publication No. WO / 2009/055783, International Patent Application Publication No. WO / 2012/0544438, International Patent Application Publication No. WO / 2010/029513, Patent Application Publication International No. WO / 2011/111007, International Patent Application Publication No. WO / 2010/077854, International Patent Application Publication No. WO / 2012/088313, International Patent Application Publication No. WO / 2012/101251, International Patent Application Publication No. WO / 2012/101252, International Patent Application Publication No. WO / 2012/101253, International Patent Application Publication No. WO / 2012/109530, and Application for Publication of International Patent No. WO / 2001/031007, International Patent Application Publication No. WO / 2009/026558, International Patent Application Publication No. WO / 2009/131740, International Patent Application Publication No. WO / 2013/166448, and Publication of International Patent Application No. WO / 2014/150983.
Talimogen laherparepvec or another HSV oncolytic may also be included for the treatment of melanoma or other cancers. Some examples of VHS oncolytic include, but are not limited to, talimogene laherparepvec (US Patent Nos. 7,223,593 and 7,537,924); OncoVEXGALV / CD (US Patent Document No. 7,981,669); OrienXOlO (Leí et al. (2013), World J. Gastroenterol., 19: 5138-5143); G207.1716; NV1020; NV12023; NV1034 and NV1042 (Vargehes etal. (2002), Cancer Gene Ther., 9 (12): 967-978).
TIMP is also included. TIMPs are endogenous tissue inhibitors of metalloproteinases (TIMPs) and are important in numerous natural processes. TIMP-3 is expressed in various cells and is present in the extracellular matrix; It inhibits all major cartilage-degrading metalloproteinases, and may play a role in the role of numerous degenerative connective tissue diseases, including rheumatoid arthritis and osteoarthritis, as well as cancer and cardiovascular conditions. The amino acid sequence of TIMP-3, and the nucleic acid sequence of a DNA encoding TIMP-3, are disclosed in US Patent No. 6,562,596, filed May 13, 2003, the disclosure of which is incorporated by reference herein. The description of TIMP mutations can be found in United States Publication Document No. 2014/0274874 and PCT Publication Document No. WO 2014/152012.
Also included are antagonistic antibodies to the receptor for the human calcitonin gene-related peptide (CGRP) and dis-specific antibody molecules that target the CGRP receptor and other headache targets. Additional information regarding these molecules can be found in PCT Application document No. WO 2010/075238.
In addition, a compromising dispecific antibody can be used in the device.
319 T lymphocytes (BiTe), for example Blinotumomab. Alternatively, an APJ large molecule antagonist, eg apelin or analogs thereof, may be included in the device. Information regarding such molecules can be found in PCT Publication Document No. WO 2014/099984.
In certain embodiments, the medicament comprises a therapeutically effective amount of an anti-thymic stromal lymphopoietin antibody (TSLP) or against the TSLP receptor. Some examples of anti-TSLP antibodies that can be used in such embodiments include, but are not limited to, those described in US Patent Nos. 7,982,016, and 8,232,372, and Publication Document United States No. 2009/0186022. Some examples of anti-TSLP receptor antibodies include, but are not limited to, those described in US Patent No. 8,101,182. In particularly preferred embodiments, the medicament comprises a therapeutically effective amount of the anti-TSLP antibody designated A5 in US Patent No. 7,982,016.
XXV. Additional aspects
The drug delivery devices, mounts, mechanisms, components, features, functionalities, manufacturing methods, and methods of use described above can incorporate various aspects of the drug delivery devices, mounts, mechanisms, components, features, functionalities, manufacturing methods, and methods of use described in the following documents, each of which is incorporated in its entirety for all purposes: United States Patent No. 8,939,935; United States Patent Application Publication No. 2013/0060233; United States Patent Application Publication No. 2013/0066274; United States Patent Application Publication No. 2013/0237916; United States Patent Application Publication No. 2014/0200510; United States Patent Application Publication No. 2014 / 0288511A1; United States Patent Application Publication No. 2015/0290390; United States Patent Application Publication No. 2015 / 0374919A1; United States Patent Application Publication No. 2015/0209505; United States Patent Application Publication No. 2015/0297827; United States Patent Application Publication No. 2015/0359965; United States Patent Application Publication No. 2015/0190588; United States Patent Application Publication No. 2015/0217045; United States Patent Application Publication No. 2015/0057613; United States Patent Application Publication No. 2014/0296787; United States Provisional Patent Application No. 62 / 094,395 entitled "DRUG DELIVERY DEVICE WITH PROXIMITY SENSOR"; US Provisional Patent Application No. 62 / 114,200 entitled "ROTATIONALLY BIASED INSERTION MECHANISM FOR A DRUG DELIVERY PUMP"; Provisional Patent Application
320 United States No. 62 / 117,420 entitled “DRUG DELIVERY DEVICE WITH VACUUM ASSISTED SECUREMENT AND / OR FEEDBACK”; United States Provisional Patent Application No. 62 / 127,021 entitled "DEVICE AND METHOD FOR MAKING ASEPTIC CONNECTIONS"; US Provisional Patent Application No. 62 / 130,318 entitled "MULTI-FUNCTION DRIVE MECHANISMS FOR CONTROLLED DRUG DELIVERY PUMPS"; United States Provisional Patent Application No. 62 / 266,788 entitled "DRUG DELIVERY STORAGE DEVICE AND SYSTEM"; United States Provisional Patent Application No. 62 / 293,556 filed on February 10, 2016 titled "DRUG DELIVERY DEVICE"; United States Provisional Patent Application No. 62 / 133,690 entitled "ROTATIONALLY BIASED INSERTION MECHANISM FOR A DRUG DELIVERY PUMP"; United States Provisional Patent Application No. 62 / 201,456 entitled "MULTI-FUNCTION DRIVE MECHANISMS FOR CONTROLLED DRUG DELIVERY PUMPS"; US Provisional Patent Application No. 62 / 147,435 entitled "MULTI-FUNCTION DRIVE MECHANISMS FOR CONTROLLED DRUG DELIVERY PUMPS"; United States Provisional Patent Application No. 62 / 134,226 entitled "MULTI-FUNCTION DRIVE MECHANISMS FOR CONTROLLED DRUG DELIVERY PUMPS"; United States Provisional Patent Application No. 62 / 147,403 entitled "ROTATIONALLY BIASED INSERTION MECHANISM FOR A DRUG DELIVERY PUMP"; United States Provisional Patent Application No. 62 / 220,754 entitled "CONTROLLED DELIVERY DRIVE MECHANISMS FOR DRUG DELIVERY PUMPS"; United States Provisional Patent Application No. 62 / 290,064 entitled "ASEPTIC CONNECTIONS FOR DRUG DELIVERY DEVICES"; US Provisional Patent Application No. 62 / 201,468 titled "DRUG DELIVERY PUMPS HAVING MULTIPLE CHAMBERS"; United States Provisional Patent Application No. 62 / 262,666 entitled "SYSTEMS FOR THE CONTROL OF DRUG DELIVERY PUMPS BASED ON INPUT DATA"; United States Provisional Patent Application No. 62 / 241,906 entitled "FILL-FINISH CARRIERS FOR DRUG CONTAINERS"; United States Provisional Patent Application No. 62 / 262,683 entitled "SYSTEMS AND METHODS FOR CONTROLLED DRUG DELIVERY PUMPS"; United States Provisional Patent Application No. 62 / 204,866 titled "AUTOMATIC DRUG INJECTORS AND ASSOCIATED DEVICES INCORPORATING DATA RECORDING, TRANSMISION, AND RECEIVING"; United States Provisional Patent Application No. 62 / 239,116 entitled "AUTOMATIC INJECTORS FOR INJECTABLE CARTRIDGES INCORPORATING SIMPLIFIED LOADING OF CARTRIDGES"; United States Provisional Patent Application No. 62 / 206,503 titled "ARCUATE DRIVE MECHANISMS FOR AUTOMATIC INJECTORS"; US Provisional Patent Application No. 62 / 278,028 titled "MEDICAL DEVICE INCORPORATING ADHESIVE WITH STIMULANT SENSITIVE BONDING STRENGTH"; International Patent Application Publication No. WO / 2015/061386; Publication of International Patent Application No.
321
WO / 2015/061389; International Patent Application Publication No. WO / 2015/187793; International Patent Application Publication No. WO / 2015/187797; International Patent Application Publication No. WO / 2015/187799; International Patent Application Publication No. WO / 2015/187802; International Patent Application Publication No. WO / 2015/187805;
International Patent Application Publication No. WO / 2016/003813; International Patent Application No. PCT / US2016 / 017534 entitled “ROTATIONALLY BIASED INSERTION MECHANISM FOR A DRUG DELIVERY PUMP”; International Patent Application No. PCT / US2016 / 017534 entitled “ROTATIONALLY BIASED INSERTION MECHANISM FOR A DRUG DELIVERY PUMP; International Patent Application No. PCT / US2015 / 052311 titled 10 “CONCENTRIC BARREL DRUG CONTAINERS AND DRUG DELIVERY PUMPSTHATALLOW
MIXING AND DELIVERY ”; International Patent Application No. PCT / US2015 / 052367 entitled "SEQUENTIAL CHAMBER DRUG DELIVERY PUMPS FOR DRUG MIXING AND DELIVERY"; International Patent Application No. PCT / US2015 / 047487 entitled "SKIN SENSORS FOR DRUG DELIVERY DEVICES"; International Patent Application No. PCT / US2015 / 052815 entitled "RIGID NEEDLE INSERTION MECHANISM FOR A DRUG DELIVERY PUMP"; International Patent Application No. PCT / US2015 / 047503 entitled "SENSOR SYSTEMS FOR DRUG DELIVERY DEVICES"; International Patent Application No. PCT / US2016 / 021585 entitled DRIVE MECHANISMS FOR DRUG DELIVERY PUMPS ”; International Patent Application No. PCT / US2016 / 020486 entitled DEVICE AND METHOD FOR MAKING ASEPTIC -20 CONNECTIONS ”; International Patent Application No. PCT / US15 / 29485 titled AUTOINJECTOR WITH SHOCK REDUCING ELEMENTS ”. In addition, the drug delivery devices, mounts, mechanisms, components, features, functionalities, manufacturing methods, and methods of use described in any of the Incorporated by Reference disclosures listed above may include a container partially or completely filled with one or more of the drugs described above, including, for example, a specific antibody against PCSK9, a G-CSF, an antibody to sclerostin, or an antibody to CGRP.
In the specification, the objective has been to describe the preferred embodiments of the disclosure without limiting the disclosure to any specific embodiment or collection of features. Various changes and modifications can be made in the described and illustrated embodiments without departing from the present disclosure. The disclosure of each patent document and scientific document, computer program, and algorithm referenced in this specification is incorporated by reference in its entirety.
322
Contents9
168 sheets
Sheet 1 Sheet 2 Sheet 3 Sheet 4 Sheet 5 Sheet 6 Sheet 7 Sheet 8 Sheet 9 Sheet 10 Sheet 11 Sheet 12 Sheet 13 Sheet 14 Sheet 15 Sheet 16 Sheet 17 Sheet 18 Sheet 19 Sheet 20 Sheet 21 Sheet 22 Sheet 23 Sheet 24 Sheet 25 Sheet 26 Sheet 27 Sheet 28 Sheet 29 Sheet 30 Sheet 31 Sheet 32 Sheet 33 Sheet 34 Sheet 35 Sheet 36 Sheet 37 Sheet 38 Sheet 39 Sheet 40 Sheet 41 Sheet 42 Sheet 43 Sheet 44 Sheet 45 Sheet 46 Sheet 47 Sheet 48 Sheet 49 Sheet 50 Sheet 51 Sheet 52 Sheet 53 Sheet 54 Sheet 55 Sheet 56 Sheet 57 Sheet 58 Sheet 59 Sheet 60 Sheet 61 Sheet 62 Sheet 63 Sheet 64 Sheet 65 Sheet 66 Sheet 67 Sheet 68 Sheet 69 Sheet 70 Sheet 71 Sheet 72 Sheet 73 Sheet 74 Sheet 75 Sheet 76 Sheet 77 Sheet 78 Sheet 79 Sheet 80 Sheet 81 Sheet 82 Sheet 83 Sheet 84 Sheet 85 Sheet 86 Sheet 87 Sheet 88 Sheet 89 Sheet 90 Sheet 91 Sheet 92 Sheet 93 Sheet 94 Sheet 95 Sheet 96 Sheet 97 Sheet 98 Sheet 99 Sheet 100 Sheet 101 Sheet 102 Sheet 103 Sheet 104 Sheet 105 Sheet 106 Sheet 107 Sheet 108 Sheet 109 Sheet 110 Sheet 111 Sheet 112 Sheet 113 Sheet 114 Sheet 115 Sheet 116 Sheet 117 Sheet 118 Sheet 119 Sheet 120 Sheet 121 Sheet 122 Sheet 123 Sheet 124 Sheet 125 Sheet 126 Sheet 127 Sheet 128 Sheet 129 Sheet 130 Sheet 131 Sheet 132 Sheet 133 Sheet 134 Sheet 135 Sheet 136 Sheet 137 Sheet 138 Sheet 139 Sheet 140 Sheet 141 Sheet 142 Sheet 143 Sheet 144 Sheet 145 Sheet 146 Sheet 147 Sheet 148 Sheet 149 Sheet 150 Sheet 151 Sheet 152 Sheet 153 Sheet 154 Sheet 155 Sheet 156 Sheet 157 Sheet 158 Sheet 159 Sheet 160 Sheet 161 Sheet 162 Sheet 163 Sheet 164 Sheet 165 Sheet 166 Sheet 167 Sheet 168
52 members in 12 offices
Priority claims7
| Document | Office | Kind | Date |
|---|---|---|---|
| 62294842 | United States of America | – | |
| 201662294842 | United States of America | P | |
| 62297718 | United States of America | – | |
| 201662297718 | United States of America | P | |
| 62320438 | United States of America | – | |
| 201662320438 | United States of America | P | |
| 2017017627 | United States of America | W |
Members52
| Document | Office | Kind | |
|---|---|---|---|
| CA3014063A1 | Canada | A1 | |
| WO2017139741A1 | World Intellectual Property Organization (WIPO) | A1 | |
| UY37122A | Uruguay | A | |
| TW201733562A | Taiwan Province of China | A | |
| CA3020337A1 | Canada | A1 | |
| WO2017177094A2 | World Intellectual Property Organization (WIPO) | A2 | |
| WO2017177094A3 | World Intellectual Property Organization (WIPO) | A3 | |
| UY37200A | Uruguay | A | |
| TW201742644A | Taiwan Province of China | A | |
| AR107607A1 | Argentina | A1 | |
| AR108110A1 | Argentina | A1 | |
| AU2017217994A1 | Australia | A1 | |
| AU2017248238A1 | Australia | A1 | |
| MX2018009826AThis record | Mexico | A | |
| EP3413953A1 | European Patent Office (EPO) | A1 | |
| US2019022306A1 | United States of America | A1 | |
| MX2018012290A | Mexico | A | |
| EP3439715A2 | European Patent Office (EPO) | A2 | |
| JP2019509787A | Japan | A | |
| JP2019513463A | Japan | A | |
| US2020316291A1 | United States of America | A1 | |
| EP3439715B1 | European Patent Office (EPO) | B1 | |
| TWI725120B | Taiwan Province of China | B | |
| EP3834864A1 | European Patent Office (EPO) | A1 | |
| TW202123917A | Taiwan Province of China | A | |
| JOP20170088B1 | Jordan | B1 | |
| US11129936B2 | United States of America | B2 | |
| TWI750163B | Taiwan Province of China | B | |
| US2021402083A1 | United States of America | A1 | |
| US11266777B2 | United States of America | B2 | |
| JP2022062118A | Japan | A | |
| JP7074684B2 | Japan | B2 | |
| AU2017217994B2 | Australia | B2 | |
| AU2017248238B2 | Australia | B2 | |
| AU2022203334A1 | Australia | A1 | |
| US2022218900A1 | United States of America | A1 | |
| JP2022119810A | Japan | A | |
| JOP20170042B1 | Jordan | B1 | |
| AU2022224838A1 | Australia | A1 | |
| TWI796651B | Taiwan Province of China | B | |
| AU2022203334B2 | Australia | B2 | |
| MX2023014313A | Mexico | A | |
| JP2024020513A | Japan | A | |
| JP7434380B2 | Japan | B2 | |
| AU2024200795A1 | Australia | A1 | |
| AR127862A2 | Argentina | A2 | |
| AU2022224838B2 | Australia | B2 | |
| JP2024099647A | Japan | A | |
| JP7554229B2 | Japan | B2 | |
| US12201809B2 | United States of America | B2 | |
| SA523442889B1 | Saudi Arabia | B1 | |
| US12433994B2 | United States of America | B2 |
Numbers
- Publication
- 2018009826
- Application
- 9826
Titles2
- Spanish
- DISPOSITIVO DE ADMINISTRACION DE FARMACOS, METODO DE FABRICACION Y METODO DE USO.
- English
- DRUG DELIVERY DEVICE AND METHOD OF MANUFACTURE.
Classification
- CPC, 9
- A61M5/14248
- A61M5/142
- A61M5/14566
- A61M5/315
- A61M2005/2481
- A61M2205/3368
- A61M2205/35
- A61M2005/14252
- A61M2005/14268
- IPC, 3
- A61M5 142
- A61M5 145
- A61M5 315