Wireless electrocardiograph system
Abstract
A chest assembly for detecting electrical signals from a patient's heart, comprising: an electrode retention section having a plurality of electrode connectors for releasably connecting to the electrodes; a chest assembly connector attached to the electrode retention section; and a sensor pin on the connector of the chest assembly to complete a circuit within the electronic unit of the body, where the sensor pin is configured so that the electronic unit of the body is activated when the sensor pin completes the circuit inside the unit body electronics, inserting the chest assembly connector into a chest assembly port of the body electronic unit.

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Projected expiry passed 26 November 2022, 3.8 years ago.
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35 claims: 9 independent, 26 dependent
- 1ES 2 311 643 T3 REIVINDICACIONES 1. Un conjunto de pecho para detectar señales eléctricas del corazón de un paciente, que comprende:una sección de retención de electrodos que tiene una pluralidad de conectores de electrodos para conectarse de manera liberable a los electrodos;un conector del conjunto del pecho unido a la sección de retención de los electrodos;y una patilla sensora sobre el conector del conjunto del pecho para completar un circuito dentro de la unidad electrónica del cuerpo, donde la patilla sensora está configurada de manera que se activa la unidad electrónica del cuerpo cuando la patilla sensora completa el circuito dentro de la unidad electrónica del cuerpo, insertando el conector del conjunto del pecho en un puerto del conjunto del pecho de la unidad electrónica del cuerpo.
- 2El conjunto del pecho de la reivindicación 1, en el que la sección de retención de electrodos incluye al menos un brazo extensible.
- 3El conjunto del pecho de la reivindicación 2, en el que la sección de retención de electrodos comprende además una sección arqueada, un tendido lineal y un brazo de extensión.
- 4El conjunto del pecho de la reivindicación 1, 2 o 3, en el que los conectores de electrodos están configurados de manera un electrodo pueda ser posicionado en el lado derecho del pecho del paciente, aproximadamente a nivel del primer y segundo espacios intercostales, un electrodo puede quedar situado en el lado izquierdo del pecho del paciente, aproximadamente a nivel del primer y segundo espacios intercostales, un electrodo puede estar posicionado en el centro del pecho del paciente, aproximadamente al nivel del cuarto y quinto espacio intercostal, y dos electrodos pueden quedar posicionados en el lado izquierdo del torso del paciente.
- 5El conjunto del pecho de la reivindicación 3, en el que la sección de retención de electrodos está conectada al conector del conjunto del pecho, por medio de una sección lineal.
- 6El conjunto del pecho de la reivindicación 5, en el que la sección arqueada se apoya sobre la sección lineal, un primer brazo extensible se une a la sección arqueada, y un conector de electrodo se une al primer brazo extensible, una sección de transición se apoya sobre la sección arqueada y a un conector de electrodo unido a la sección de transición, un tendido lineal se apoya sobre la sección de transición y un conector de electrodos se une al tendido lineal, y un segundo brazo extensible y un brazo de extensión se unen al tendido lineal, un conector de electrodo se une al segundo brazo de extensión, y un conector de electrodo se une al segundo brazo extensible.
- 7El conjunto del pecho de la reivindicación 3, en el que el conjunto del pecho se conecta a un transmisor de telemetría a través de un conjunto adaptador.
- 8El conjunto del pecho de la reivindicación 3, en el que el conjunto del pecho se conecta a un monitor electrocardiográfico a través de un conjunto adaptador.
- 9El conjunto del pecho de la reivindicación 3, en el que el conector del conjunto del pecho incluye una pluralidad de elementos eléctricamente conductores suficientemente separados para impedir el arco eléctrico a través de los elementos eléctricamente conductores.
- 10El conjunto del pecho de la reivindicación 9, en el que el conector del conjunto del pecho incluye una pluralidad de nervaduras para impedir que los elementos eléctricamente conductores hagan contacto con objetos cuando el conector del conjunto del pecho no esté fijado dentro de la unidad electrónica del cuerpo.
- 11El conjunto del pecho de la reivindicación 9, en el que los elementos eléctricamente conductores están espaciados para permitir que el conjunto del pecho soporte un shock de desfibrilación.
- 12Un conjunto del pecho, como se reivindica en la reivindicación 1, que comprende:una capa base que tiene un primer lado y un segundo lado, el primer lado unido a una pluralidad de elementos eléctricamente conductores, el segundo lado unido a una capa de apantallamiento;una primera capa de aislamiento colocada por encima de la capa base;y una segunda capa de aislamiento colocada por debajo de la capa base.
- 13El conjunto del pecho de la reivindicación 12, en el que los elementos eléctricamente conductores se conectan a conectores de los electrodos y a un conector del conjunto del pecho.
- 14El conjunto del pecho de la reivindicación 12 o 13, que comprende además una capa de apantallamiento con una construcción de rejilla con un diseño en X. ES 2 311 643 T3
- 15El conjunto del pecho de la reivindicación 12, 13 o 14, en el que la capa de apantallamiento comprende una sola capa de material dieléctrico.
- 16El conjunto del pecho de la reivindicación 12, 13 o 14, en el que la capa de apantallamiento comprende múltiples capas de material dieléctrico.
- 17Un conjunto del pecho como se reivindica en la reivindicación 1, en el que:el conjunto del pecho es un conjunto precordial, la sección de retención de electrodos es una sección flexible de retención de electrodos conectada al conector del conjunto precordial por medio de una sección lineal, la sección de retención de electrodos está unida de manera liberable a una pluralidad de conectores de electrodos, y la sección de retención de electrodos comprende al menos un brazo de extensión, una pluralidad de secciones arqueadas y una pluralidad de segmentos de transición.
- 18El conjunto del pecho de la reivindicación 17, en el que una primera sección arqueada se apoya sobre la sección lineal, una primera sección de transición se apoya sobre una primera sección arqueada y un conector de electrodo se une al primer segmento de transición, una segunda sección de transición se conecta al primer brazo de extensión, una segunda sección arqueada se apoya sobre la primera sección de transición, una segunda sección de transición se apoya sobre la segunda sección arqueada y un conector de electrodo se une a la segunda sección de transición y un conector de electrodo se une a la segunda sección de transición, un segundo brazo de extensión se conecta a la segunda sección de transición y un conector de electrodo se une al segundo brazo de extensión, una tercera sección arqueada se apoya sobre la segunda sección de transición, un tercer segmento de transición se apoya sobre la tercera sección arqueada y un electrodo conector se une al tercer segmento de transición, y una cuarta sección arqueada se apoya sobre el tercer segmento de transición y un conector de electrodo se une a la cuarta sección arqueada.
- 19El conjunto del pecho de la reivindicación 17 o 18, en el que el conjunto precordial se conecta a un transmisor de telemetría a través de un conjunto adaptador.
- 20El conjunto del pecho de la reivindicación 17 o 18, en el que el conjunto precordial se conecta a un monitor electrocardiográfico a través de un conjunto adaptador.
- 21El conjunto del pecho de cualquiera de las reivindicaciones 17 a 20, en el que el conector del conjunto precordial incluye una pluralidad de elementos eléctricamente conductores, suficientemente separados para impedir el arco eléctrico a través de los elementos eléctricamente conductores.
- 22El conjunto del pecho de la reivindicación 21, en el que el conjunto precordial incluye una pluralidad de nervaduras para impedir que los elementos eléctricamente conductores hagan contacto con objetos, cuando el conector del conjunto precordial no está fijado dentro de la unidad electrónica del cuerpo.
- 23El conjunto del pecho de la reivindicación 21 o 22, en el que el conector del conjunto del pecho incluye una pluralidad de pestañas elásticas y al menos una lengüeta correspondiente al menos a una hendidura en el puerto del conjunto del pecho.
- 24El conjunto del pecho de la reivindicación 23, en el que los elementos eléctricamente conductores están espaciados para permitir que el conjunto precordial soporte un shock de desfibrilación.
- 25Una unidad electrónica del cuerpo, para ser utilizada en un sistema de monitorización de la actividad cardiaca en un paciente, que comprende:un puerto del conjunto del pecho par recibir de manera liberable un conector de conjunto del pecho, unido a un conjunto del pecho, incluyendo el conector del conjunto del pecho una patilla sensora que completa un circuito dentro de la unidad electrónica del cuerpo cuando se inserta el conector del conjunto del pecho en un puerto del conjunto del pecho, donde las señales eléctricas detectadas del corazón del paciente se transmiten a la unidad electrónica del cuerpo a través del conjunto del pecho, donde la alimentación de la unidad electrónica del cuerpo se activa cuando la patilla sensora completa el circuito dentro de la unidad electrónica del cuerpo.
- 26La unidad electrónica del cuerpo de la reivindicación 25, que comprende además un interfaz de usuario para comunicar información al usuario.
- 27La unidad electrónica del cuerpo de la reivindicación 26, en la que la información pertenece al estado de funcionamiento del sistema.
- 28La unidad electrónica del cuerpo de la reivindicación 26 o 27, en el que la información pertenece a la orden para emparejar la unidad electrónica del cuerpo con una estación base. ES 2 311 643 T3
- 29La unidad electrónica del cuerpo de cualquier de las reivindicaciones 25 a 28, en la que la unidad electrónica del cuerpo es capaz de realizar una función de conductor desconectado para supervisar continuamente la integridad de las conexiones entre al menos un conector de electrodo unido al conjunto del pecho, y al menos un electrodo unido al paciente.
- 30La unidad electrónica del cuerpo de cualquiera de las reivindicaciones 25 a 29, en la que la unidad electrónica del cuerpo es capaz de realizar una función de auto-comprobación para supervisar la integridad de las funciones del sistema.
- 31La unidad electrónica del cuerpo de cualquiera de las reivindicaciones 25 a 29, que comprende además una resistencia conectada al puerto del conjunto del pecho, para impedir que entre una corriente eléctrica excesiva en la unidad electrónica del cuerpo, permitiendo con ello que la unidad electrónica del cuerpo soporte un shock de desfibrilación.
- 32La unidad electrónica del cuerpo de cualquiera de las reivindicaciones 25 a 31, que comprende además al menos una batería que es compatible con un puerto de batería en la unidad electrónica del cuerpo, y un puerto de batería en una estación base.
- 33La unidad electrónica del cuerpo de cualquiera de las reivindicaciones 25 a 32, que comprende además un puerto para recibir un aparato para emparejar una estación base con la unidad electrónica del cuerpo.
- 34La unidad electrónica del cuerpo de la reivindicación 33, en la que el aparato es una llave ficha.
- 35Un sistema para la transmisión inalámbrica de señales fisiológicas desde un paciente a un monitor, que comprende un conjunto del pecho como se reivindica en cualquiera de las reivindicaciones 1 a 24 y una unidad electrónica del cuerpo como se reivindica en cualquiera de las reivindicaciones 25 a 34, donde el conjunto del pecho y la unidad electrónica del cuerpo están conectadas por medio del conector del conjunto del pecho y del puerto del conjunto del pecho.
Independent claims35
80 paragraphs in 4 sections, as filed
ES 2 311 643 T3
DESCRIPTION
Wireless electrocardiography system.
A portion of the disclosure of this patent document contains material that is subject to copyright protection. The owner of the rights has no objection to the reproduction in facsimile by anyone, of the patent document or of the patent disclosure, as it appears in the patent files or records of the Patent and Trademark Office, but on the other part reserves all copyrights, whatever they may be.
Related requests
This international application claims the priority, of the United States Application with serial number 09 / 998,733 for a Wireless eCg System, filed on November 30, 2001, the disclosure and content of which is incorporated herein by reference in its entirety. .
Field of the invention
The present invention relates to a cardiac monitoring system and, more particularly, to a wireless electrocardiography (ECG) system.
Background of the invention
An electrocardiographic (ECG) system monitors the electrical activity of the heart in a patient. Conventional ECG systems use lead terminals or electrodes placed on a patient at specific locations to detect electrical impulses generated by the heart during each beat. In response to sensing electrical impulses from the heart, the electrodes produce electrical signals indicative of cardiac activity. Typically, these electrical signals are transferred directly from the electrodes to a stationary ECG monitor, through multiple cables or wires. The ECG monitor performs various signal processing and calculation operations to convert raw electrical signals into relevant information that can be displayed on a monitor or printed for review by the physician.
Doctors have used ECG systems to monitor a patient's heart activity for decades. Currently, there are several different systems that use ECG signals to monitor the patient's heart activity. However, these systems are generally stationary and are not developed or suitable for portable use. Although portable telemetry systems exist, they are not a direct replacement for stationary ECG systems. Furthermore, because conventional systems use multiple cables or wires, and are cumbersome and uncomfortable for the patient, they require a significant amount of commissioning. Therefore, there is a need for an ECG system that solves the aforementioned problems.
Brief summary of the invention
The present invention relates to a wireless ECG system, which is universally compatible with existing or conventional ECG monitors. The ECG system comprises a chest kit, an electronic body unit, and a base station. The chest assembly connects electrodes specifically located on a patient's body to detect electrical signals from the patient's heart. The electrical signals are detected by the whole chest, thus providing an analysis of the heart of up to “7 leads”. Alternatively, the chest assembly can be augmented with a precordial assembly that connects to electrodes specifically located on the patient's body, thus providing a "12-lead" analysis of the heart.
Viewed from a first aspect, the present invention provides a chest assembly for detecting electrical signals from a patient's heart, comprising:
an electrode retention section, having a plurality of electrode connectors for releasably connecting to the electrodes;
a chest assembly connector attached to the electrode retention section; and a sensing pin on the chest assembly connector, for completing the circuit within an electronic body unit, by inserting the chest assembly connector into a port on the chest assembly of the electronic body unit.
Viewed from a second aspect, the present invention provides an electronic body unit for use in a monitoring system for cardiac activity in a patient, comprising:
a chest assembly to removably receive a chest assembly connector attached to the chest assembly, the chest assembly connector including a sensing pin that completes a circuit within the electronic body unit, when the chest assembly connector is inserted into the port of the chest assembly, in
ES 2 311 643 T3 which the electrical signals detected from the heart of a patient are transmitted to the electronic unit of the body through the whole of the chest.
The electrical signals are transmitted through the chest assembly and the precordial assembly to the electronic body unit, which can be removably attached to the patient by means of a bracelet. The electronic body unit can transmit the electrical signals to the base station, via radio transmission. The base station transmits the electrical signals to a conventional ECG monitor through standard wiring, which, in turn, processes or transforms the electrical signals into useful information that can be displayed on the ECG monitor for review by a doctor.
The ECG system eliminates the cables that normally link the ECG patient to an ECG monitor, replacing conventional cables with a radio link. The present invention is light in weight and portable, thus providing increased comfort and mobility for the patient. Furthermore, the present invention requires shorter start-up times and is more convenient for healthcare professionals to use than conventional ECG systems.
These, as well as other advantages, details, embodiments, features, and novel objects of the present invention, will be more apparent to those skilled in the art from the following detailed description of the invention, the appended claims, and the drawings. which are attached, which are listed below, and which are useful in explaining the invention.
Brief description of the drawings
The foregoing aspects and many of the advantages of the present invention will be readily appreciated with reference to the following detailed description of the preferred embodiments, when taken in conjunction with the accompanying drawings, in which:
Figure 1 is a perspective view of an exemplary embodiment of the ECG system;
Figure 2 is a cross-sectional view of the chest assembly and the precordial assembly;
Figure 3 is a top view of an exemplary embodiment of the chest assembly;
Figure 4 is a top view of an exemplary embodiment of the precordial assembly;
Figure 5 is a perspective view of an exemplary embodiment of the electronic body unit;
Figure 6 is a top view of an exemplary embodiment of the connectors of the assembly;
Figure 7 is a front view of an exemplary embodiment of the electronic body unit;
Figure 7a is an example embodiment of the user interface of the electronic body unit;
Figure 8 is a block diagram of an exemplary embodiment of the transmitter;
Figure 9a is a perspective view of an exemplary embodiment of the base station, used in conjunction with the token key;
Figure 9b depicts the electronic body unit used in conjunction with the token-shaped key;
Figure 10 is a perspective view of an exemplary embodiment of the base station;
Figure 11 is a front view of an exemplary embodiment of the base station;
Figure 11a is an exemplary embodiment of the base station user interface;
Figure 12 is a block diagram of an exemplary embodiment of the receiver;
Figure 13 is a perspective view of an exemplary embodiment of the base station;
Figure 14 is an exemplary embodiment of the adapter assembly;
Figure 15 is another example embodiment of the adapter assembly;
Figure 16 is another example embodiment of the adapter assembly; Y
Figure 17 is a flow chart of an exemplary embodiment for the operation of the ECG system.
ES 2 311 643 T3
Description of the preferred embodiment
For a better understanding of the present invention, reference should be made to the following detailed description, taken in conjunction with the appended claims and the accompanying drawings. Briefly, the present invention relates to a portable wireless eCg system. Referring to Figure 1, the ECG system 10 comprises a chest assembly 12, a body electronics unit 14, and a base station 16.
Chest assembly 12 is a one-piece flexible circuit, which connects to a plurality of electrode connectors 18, which are individually indicated 18a, 18b, 18c, 18d, and 18e. Electrode connectors 18 have releasable connections that connect to electrodes 20, which are individually indicated 20a, 20b, 20c, 20d, and 20e. Preferably, the electrode connectors 18 have push-on terminals that connect the electrodes 20 that have snap-on connectors. Each electrode connector 18 connects to an electrically conductive or trace element to transmit electrical signals. The electrically conductive or trace elements run along the chest assembly 12 and are connected to a connector 21 on the chest assembly.
Referring to Figure 2, the chest assembly 12 has outer layers 22, 24 that are constructed of a light weight and reasonably moisture resistant material, such as the Sontara<sup>®</sup> DuPont or other suitable fabric. The adhesive layers 26, 28 fix the insulating layers 30, 32 to the outer layers 22, 24 respectively. The insulating layers 30, 32 are constructed of Mylar® (polyester) film or other suitable insulating material. Adhesive layers 34, 36 secure insulating layers 30, 32 to base layer 38. Base layer 38 is preferably constructed of Mylar film and has a first side 40 and a second side 42. Electrically conductive or trace elements, which are connected to electrode connectors 18, are located on the first side 40 of base layer 38. One such conductor or trace elements is illustrated as 39. A shield layer 44, for To reduce any external interference or radio frequency noise with the chest assembly 12, it is located on a second side 42 of the base layer 38. Shielding layer 44 may be constructed of one or more layers of dielectric, or electrically or magnetically conductive material. The back of the electrode connector 18 may also be covered with Mylar to further isolate the assembly 12 from the chest and prevent an externally applied electrical potential from entering the ECG system. The shielding layer preferably comprises a grid with an X pattern.
Referring back to Figure 1, the chest assembly 12 is attached to five electrodes 20 and provides a means for generally positioning the electrodes on the patient, thus providing up to "7-lead" analysis of the electrical activity of the heart. The electrode connectors 18 are preferably color-coded and labeled to ensure that the chest assembly 12 is properly positioned on the patient and connected to the appropriate electrodes 20. For example, connectors 18a, 18b, 18c, 18d, 18e are labeled RL, LA, LL, RA, and V, respectively. The chest assembly 12 is constructed so that the electrode connector RA is connected to an electrode positioned on the right side of the patient's chest approximately at the level of the first and second intercostal spaces, the electrode connector LA is connected to a positioned electrode on the left side of the patient's chest approximately at the level of the first and second intercostal spaces, The RL and LL electrode connectors are connected to electrodes positioned on the left side of the chest of the patient's torso, and the V electrode connector is connected to an electrode positioned in the center of the patient's chest, approximately at the level of the fourth and fifth intercostal spaces. The chest assembly 12 is designed so that it is centered on the chest, below the patient's clavicle.
Referring to Figure 3, the chest assembly 12 is configured to provide flexible positioning of the chest assembly 12 on the patient. Figure 3 is for illustrative purposes only, and therefore chest assembly 12, as depicted in Figure 3, is not limited to any particular shape or configuration. The chest assembly 12 has a linear section or tail 46 that extends from the chest assembly connector 21. Referring back to Figure 1, the tail 46 has an attachment means 46a that allows the tail 46 to extend to either side of the patient. These fixing means 46a can be any suitable mechanical device, although the most preferable is an adhesive or a clamp. Returning to reference to Figure 3, glue 46 flows into electrode retention section 47. Electrode retention section 47 has arcuate section 48. There is a first extensible arm 50 that is attached to the arcuate section 48. The electrode connector RA is attached to the first extensible arm 50. The arcuate section 48 flows into the transition section 52. Electrode connector LA is attached to transition section 52. Transition section 52 flows into linear array 54. Electrode connector RL is attached to linear array 54. A second extension arm 56 and extension arm 58 are attached to linear array 54. The electrode connector V is attached to the second extension arm 58 and the electrode connector LL is attached to the second extension arm 56.
The extension arms 50, 56 are stamped in a serpentine design. Extendable arms 50, 56 comprise polypropylene or polyethylene fabric, Kapton, Mylar, or other flexible non-memory materials. The extendable arms 50, 56 are extended, if necessary, lengthening the coil pattern. When they do, part or all of the extension arm is extended. When only one part of the extendible arm is extended, the other part remains folded. The extendable arms 50, 56 allow for the necessary extension so that the chest assembly 12 can accommodate patients of different sizes and also allow movement of the patient while wearing the chest assembly 12. The extendable arm 58 allows flexible positioning of the electrode connector V in the center of the patient's chest, for example by positioning the electrode position V1, V2 or V3. In some cases, the healthcare professional may wish not to use the extension arm 58 to take electrocardiographic measurements.
ES 2 311 643 T3
Thus, to keep the extension arm 58 attached to the linear array 58 and to ensure that the extension arm 58 does not interfere with the positioning and positioning of the chest assembly 12, the extension arm 58 is stamped with a perforated seam connecting the extension arm. 58 with the linear run 54, over the entire length of the extension arm 58. If the health care practitioner wishes to use the extendable arm 58, the perforated seam remains intact so that the extendable arm 58 can be selectively selected on the patient's chest.
The chest assembly 12 can be used with a precordial assembly 60 to provide a "12-lead" analysis of the electrical activity of the heart. Similar to chest assembly 12, chest assembly 60 is a one-piece flex circuit, which connects to a plurality of electrode connectors 62. Electrode connectors 62 have releasable connections that connect to electrodes 64. Preferably, electrode connectors 62 have push-in terminals that connect to electrodes 64 that have push-in terminals. Each electrode connector 62 connects to an electrically conductive element, or trace, to transmit electrical signals from the patient's heart. Electrically conductive or trace elements run along the precordial assembly 60 and are connected to a connector 66 of the precordial assembly. The precordial assembly 60 has the construction illustrated in Figure 2.
As depicted in FIG. 1, the precordial assembly 60 is attached to six electrodes 64 that are selectively positioned on the abdomen and center of the patient's chest. The electrode connectors 62 of the precordial assembly 60 are labeled and shaped in color, preferably, to prevent the healthcare professional from improperly applying or positioning the precordial assembly on the patient. For example, connectors 62a, 62b, 62c, 62d, 62e, and 63f are labeled V1, V2, V3, V4, V5, and V6, respectively. When the precordial assembly 60 is used, the electrode connector V on the chest assembly 12 is removed from its electrode and replaced by an electrode connector on the precordial assembly 60.
As illustrated in FIG. 4, the precordial assembly 60 is configured to provide flexible positioning of the precordial assembly 60 on the patient. Figure 4 is for illustrative purposes only, and therefore the precordial assembly 60, as depicted in Figure 4, is not limited to any particular shape or configuration. The precordial assembly has a linear section or tail 68 that extends from the connector 66 of the precordial assembly. Line or tail section 68 flows into an electrode retention section 69. Electrode retention section 69 has a first arcuate section 70 having a first transition section 72. The electrode connector V2 is attached to the first transition section 72. The electrode connector V1 is attached to a first extension arm 74, connected to the first transition section 72. A second arcuate section 76 extends from the first transition section 72. A second transition section 78 abuts a second arcuate section 76 and the electrode connector V4 is attached to the second transition section 76. The electrode connector V3 is attached to a second extension arm 80, connected to the second transition section 78. A third arcuate section 82 flows from the second transition section 78. The third arched section 82 rests on a third transition section 84. The electrode connector V5 is attached to the third transition section 84. A fourth arcuate section 86 extends from the third transition section 84. Electrode V6 is attached to fourth arcuate section 86. The configuration of the precordial assembly 60 allows the healthcare professional or physician to flexibly position the electrode connectors 62 as needed, to properly position the precordial assembly 60 on the patient and to allow movement of the patient when the patient is wearing the precordial assembly 60. .
In operation, chest assembly 12 and precordial assembly 60 detect the electrical signals generated by the heart during each beat and transfer these signals to body electronics 14. When the system is operating in the "7 lead" mode (that is, when only the chest assembly 12 is being used), the body electronics unit 14 acquires signals from the RL, RA, LL, LA and V electrodes. The electronic unit 14 of the body uses the RL electrode as the ground reference. When the system is operating in the "12-lead" mode (that is, the chest assembly 12 and the precordial assembly 60 are being used) the body electronics unit 14 acquires signals from the RL, RA, LL and lA electrodes, through chest set 12 and acquires signals from electrodes V1, V2, V3, V4, V5, and V6 through precordial set 60. Alternatively, the system can monitor a different number of electrodes. For example, the healthcare professional or physician may choose to use only two electrodes to monitor the heart, seven electrodes to monitor the heart, or the like. In other words, the present system is not limited to performing a "7-lead" and "12-lead" heart analysis. In addition, to detect electrical signals from the heart, chest assembly 12 and precordial assembly 60 can be constructed to detect other vital signs of the patient, for example, pulse, rate of respiration, heart rate, temperature, etc. EEG signals and pulse oximeter signals.
Referring to Figure 5, the chest assembly 12 is connected to the body electronics unit 14 through the chest assembly connector 21. Specifically, the chest assembly connector 21 is inserted into a chest assembly port 88 in the body electronics unit 14. Similarly, the precordial assembly 60 is connected to the body electronics unit 14 through the precordial assembly connector 66. Specifically, the connector 66 of the precordial assembly (not shown) is inserted into a port 90 of the precordial assembly. Resistors are connected to chest assembly port 88 and chest assembly port 90 to prevent excessive electrical current from entering the body electronics unit 14, thereby ensuring that the body electronics unit 14 continues to function properly in the presence. from a strong electrical current originating from a defibrillator (i.e., a 5 kV defibrillation drive). The chest assembly connector 21 and the chest assembly connector 66 are specifically shaped or configured in such a way that they can prevent
ES 2 311 643 T3 connectors 21, 66 are inserted upside down into ports 88, 90 of the assembly, either misaligned or otherwise inappropriate. Furthermore, the chest assembly connector 21 is shaped or configured such that it is not compatible with the chest assembly port 90. Likewise, the precordial assembly connector 66 is shaped or configured such that it is not compatible with the chest assembly port 88. Specifically, as illustrated in Figure 5A, the body assembly connector 21 has tabs 21a specifically configured or arranged to fit in corresponding slots 21b of the chest assembly port 88. Consequently, the chest assembly connector 21 can only be connected to the chest assembly port 88 in one orientation. For example, if the tabs 21a are not aligned with the grooves 21b, the connector 21 on the chest assembly will not mate with the port 88 on the chest assembly. Likewise, the precordial assembly connector 66 has tabs (not illustrated) specifically configured or arranged to fit into corresponding slits (not illustrated) in the precordial assembly port 90.
As illustrated in Figure 6, the connector 21 and the connector 66 of the precordial assembly (not shown) have retaining clips or tabs 92, located on the sides of the connectors 21,66 to removably fix the connectors 21, 66 in ports 88, 90. However, other means may be used to removably attach connectors 21, 66 to ports 88, 90 of the assemblies, such as screws, nails, or the like. In addition, the connectors 21, 66 may have spring tabs or clips 94, located at the tip of the connectors 21, 66, to provide a bias or tension against the ports 88, 90 of the assemblies. The spring tabs or clips 94 provide the connectors 21, 66 with a secure fit within the ports 88, 90 of the assemblies, thereby reducing any play or movement of the connectors 21, 66 within the ports 88, 90 of the assemblies. . The electrically conductive elements or traces are specifically configured on the connectors 21, 66, to ensure that the electrical signals from the heart are properly transmitted to the electronic unit 14 of the body. In other words, the electrically conductive elements or traces must be sufficiently separated or insulated in some other way, to prevent the electric arc through the electrically conductive conductors. In addition, the separation of the electrically conductive or trace elements allows the whole body and the precordial assembly to withstand the shock of defibrillation. Furthermore, connectors 21, 66 have ribs 96 to prevent electrically conductive or trace elements from contacting metallic objects or the like, when connectors 21, 66 are not inserted into ports 88, 90 of the assemblies.
The chest set connector 21 has a sensing pin or ground pin 98, which completes a circuit within the body electronics unit 14 when the chest set connector 21 is plugged into the chest set port 88, thereby activating feeding and taking the electronic body unit 14 out of the "sleep mode". The sensing pin has a specific tab that matches and fits in the recess located in port 88 of the chest assembly. The sensor pin 98 serves as a means for the body electronics unit 14 to identify the chest assembly 12 and to prevent the use of other chest assemblies or portable electrocardiographic items that are not designed for use with the electronic unit 14 on the chest. body. In other words, the power to the body electronics unit 14 will not turn on unless the body electronics unit 14 identifies or recognizes the sensor pin 98 of the chest assembly 12.
The outer case of the body electronics unit 14 is constructed of a lightweight, molded plastic, such as acrylonitrile-butadiene-styrene (ABS) or other suitable material. The shape and configuration of the electronic body unit 14 is not limited to any particular shape or configuration. As illustrated in Figure 1, the body electronics unit 14 is releasably attached to the patient's arm through a band 100 on the arm, thus making the body electronics unit 14 easily accessible to the patient. The arm band 100 is wrapped around the patient's right or left arm, and attached by means of Velcro or other suitable fastening means, such as pins, snaps, or the like. The electronic body unit 14 slides under a strap or bag on the arm band 100. Referring to FIG. 7, the electronic body unit 14 has a user interface 102 and a battery 104. The user interface 102 provides information to the patient pertaining to the operating status of the system or its functionality. For example, a case of an embodiment of the user interface 102 may provide information as to whether the body electronic unit 14 is communicating or transmitting information normally to the base station 16, whether the battery 104 of the body electronic unit 14 is is charging or if the battery 104 is low, if the power to the body electronics unit 12 is on, or the body electronics unit 14 or the base station is not working properly. In addition, the user interface 102 can provide instructions on the correct order or procedure for pairing or docking the electronic body unit 14 with the base station 16. Such information can be communicated to the patient through the user interface 102 in various ways, for example with a set of LEDs, LCD, text, audible tones, etc. An exemplary embodiment of the user interface is illustrated in Figure 7a. User interface 102 is easily accessible to the patient when electronic body unit 14 is attached to arm band 100.
The battery 104 is inserted into a battery compartment 106 located at the bottom of the electronic unit 14 of the body. Battery 104 is retained in battery compartment 106 by means of locks or other suitable fastening means, such as clips, screws, or the like. Battery 104 is preferably a 3.6V lithium ion rechargeable battery. Battery 104 is easily accessible to the patient when electronic body unit 14 is attached to arm band 100.
Body electronic unit 14 controls the acquisition of ECG signals from chest assembly 12 and from precordial assembly 60. A transmitter 108, within body electronic unit 14 receives or acquires
ES 2 311 643 T3 ECG signals from chest set 12 and from precordial set 60, preferably at 3 kbps. When the system is operating in "7-lead" mode (that is, when only the chest assembly 12 is being used), the body electronics unit 14 acquires signals from the RL, RA, LL, LA and V electrodes. When the system is operating in the "12-lead mode" (that is, the chest assembly 12 and the precordial assembly 60 are being used), the body electronics unit 14 acquires signals from the RL, RA, LL, and LA electrodes. , through chest assembly 12 and acquires signals from electrodes V1 to V6 through precordial assembly 60. In addition, other vital signs of the patient can be detected by the system and transmitted to the electronic unit 14 of the body, for example the pulse, the cadence of the respiration, the heart rate, the temperature, EEG signals and impulse signals of a oximeter.
As illustrated in Figure 8, transmitter 108 comprises an application-specific integrated circuit, processor or other circuit 110, a plurality of signal channels 112, a multiplexer 114, an analog-to-digital converter (ADC) 116, a controller 118, and a radio 120. Also, fewer or different components can be used. The body electronics unit 14 has nine signal channels 112, corresponding to the ten electrodes connected to the chest assembly 12 and to the precordial assembly 60. The electrode channels 112 each comprise a connector 122, a filter 124, an amplifier 126, a Nyquist filter 128, and a track and hold circuit 130. The connectors 122 of the signal channels 112 connect to port 88 of the chest assembly, or to port 90 of the precordial assembly, depending on whether the electrode channel 112 corresponds to an electrode located in the chest assembly 12 or the precordial assembly 60. Filter 124 comprises a low pass filter to remove electromagnetic interference signals. Amplifier 126 amplifies the signals from the electrodes. Nyquist filter 128 comprises a low pass filter to remove out-of-band high frequency content from amplified signals to avoid sampling error. The track and hold circuit 130 allows the system to sample all nine electrode signals 112 at the same time or at relative times, so that there is no differential error created when these signals are later combined on an ECG monitor.
Multiplexer 114 sequentially selects signals from electrode signal channels 112, using time division multiplexing. However, one of ordinary skill in the art recognizes that other combining functions can be used. The ADC 116 converts the combined analog signals to digital signals for transmission. Preferably, controller 118 comprises a digital signal processor (DSP) that decimates digital signals to decrease the bandwidth required to transmit the signals. Radio 120 modulates digital signals with a carrier signal for transmission. In an exemplary embodiment, radio 120 includes a scrambler to receive information. Controller 118 digitally transmits the ECG data to base station 16. In addition to transmitting the ECG data, the controller 118 can transmit signals pertaining to pacemaker information, battery level information, electrode disconnection information, and other information as required. For example, vital signs such as pulse, rate of respiration, heart rate, temperature, EEG signals, and pulse signals from the oximeter can be transmitted.
The body electronics unit continuously monitors the integrity of all patient electrode connections. In the event that a lead is disconnected, the body electronics unit will send a signal to the base station, which in turn causes the base station to trigger the “lead disconnected” alarm on the ECG monitor. In addition, the body electronics unit has a self-test function that monitors the integrity of the main functions, including the microprocessor, data acquisition, internal voltage references and radio functionality. In the event that a fault is detected, the body electronics unit will capture the fault condition, stop data acquisition and transmission, and indicate that a fault has occurred via the conductor disconnected alarm.
The body electronics unit 14 functions by minimizing unwanted signals or noise. For example, there are components tailored such that subsequent application to a differential amplifier in a legacy ECG monitor system to determine a vector of the heart is accurate. ECG vectors are not formed by the ECG system 10, but rather by the system inherited from the ECG monitor. Because the ECG system 10 is essentially "in series" with the legacy ECG monitor system, any errors can produce undesirable results. One potential source of error is differential error. This differential error can be observed in the legacy ECG monitor system, when the ECG monitor forms the signals from the ECG leads by combining the individual signals from the electrodes at the input stage of the ECG monitor. This input stage comprises a difference amplifier or differential amplifier to eliminate common mode interference from the signals produced at the electrodes 20.
An artifact will be present if there is any difference in how each of the electrode signals is processed when the differential amplifier of the legacy ECG system forms the signals from the ECG leads for the ECG vectors. For example, if there is a difference in amplifier gain, a difference in phase shift associated with anti-doubling (Nyquist) filters, or a difference in how the respective track and hold circuits treat signal signals. electrodes, that differential error creates an artifact in the legacy ECG monitor system. An important technique to minimize this potential source of differential errors is to choose a Nyquist filter cutoff frequency that is very high. This is because each individual filter will perform differently in the group delay. To mitigate that difference, the frequency that this group delay will affect is much higher than the frequency of the ECG signals, which
ES 2 311 643 T3 are around 0.05 Hz to 150 Hz. By choosing a high cutoff frequency for the Nyquist filters, any decoupling between the Nyquist filter components will not affect the accuracy of the ECG signals from individual electrodes. For example, by choosing a filter cutoff frequency of 1200 Hz, this source of error is mitigated. With this solution, the ECG signals from individual electrodes are oversampled at around 3000 Hz, in order not to introduce splitting. Of course, higher filter cutoff frequencies and correspondingly higher sample rates can further reduce the error. Lower cutoff frequencies and / or sample rates can be used.
Because the signals from the electrodes are now sampled at such a high rate, these signals can be decimated to minimize the required transmission bandwidth. For example, digital samples are decimated by a factor of eight in controller 118. Higher or lower decimation rates can be used, such as decimation based on the bandwidth available for transmission, the number of electrode signals to be represented, and the Nyquist sampling rate. Referring back to FIG. 1, base station 16 receives the transmitted signals sent from body electronics unit 14. The signals are transmitted as radio signals or other signals modulated with a carrier signal. Various air interfaces can be used for transmission, such as Bluetooth or IEEE 802.11b. To establish proper communication between the body electronics unit 14 and the base station 16, the base station 16 and the body electronics unit 14 need to be paired so that the base station 16 and the body electronics unit 14 only recognize the signals. from your partner. This can be accomplished in a number of ways, including direct connection of the base station 16 and the body electronics unit 14. Preferably, a token key 132 is used to radio frequency pair or link the body electronics unit 14 with the base station 16. Referring to Figure 9a, token key 132 has a memory chip and may optionally have a plurality of tabs or pins 133 that fit within slots located in a port 134 for the token key of base station 16, and within from the slits of a port 136 of the key tab of the electronic unit 14 of the body. As illustrated in Figure 9b, token key 132 is inserted into port 134 of the base station token key, and reads and records an identification number from base station 16. Token key 132 is then removed from the port. 134 of the token key and is inserted into port 136 of the token key located in the electronic unit 14 of the body. The electronic unit 14 receives the identification number of the base station 16 from the token key 132. In turn, the token key 132 reads and registers the identification number of the electronic unit 14 of the body. Token key 132 is then removed from body electronics unit 14 and is reinserted into port 134 of token key of base station 16, whereby base station 16 confirms the presence of its own identification number on the key. card 132 and also reads the identification number of the electronic unit 14 of the body from the key card 132. The body electronics unit 14 and the base station 16 are paired. Alternatively, pairing can be accomplished by first inserting tab key 132 into body electronics unit 14, removing tab key 132 and inserting tab key 132 into base station 16, removing tab key 132 and reinserting tab 132 into the electronic unit 14 of the body. In other words, the order in which token key 132 is inserted into body electronics 14 and base station 16 is not critical to proper system operation. Referring back to FIG. 7, the user interface 102 can provide the user or healthcare professional with instructions in the correct order for pairing the electronic unit 14 with the base station 16. The use of the token key 132 allows the pairing function to take place, while the patient is wearing the electronic body unit 14. This feature eliminates the need to disconnect and reconnect the electronic unit 14 from the body when the patient needs to be connected to different ECG monitors, as a result of being moved around the hospital. The electronic unit 14 of the patient's body is repaired with a new base station using the token key 132.
Once the body electronics 14 and base station 16 are paired, the body electronics 14 and base station 16 will remain in communication with each other, as long as the token key 132 remains in port 134 for the token key of the base station 16 (or port 136 for the body electronics unit 14 token key, depending on the order of the pairing process). In other words, as soon as token key 132 is removed from base station 16, electronic unit 14 and base station 16 will interrupt or cease communication. Any specific token key 132 can be used to pair any specific base station 16 with any specific electronic body unit 14.
The outer case of the base station 16 is constructed of a lightweight, molded plastic, such as acrylonitrile-butadiene-styrene (ABS) or other suitable material. The shape and configuration of base station 16 is not limited to any particular shape or configuration. Base station 16 is releasably attached to an ECG monitor 138, through suitable means, such as Velcro®, double interlock tapes, double sided foam tape, or the like. Preferably, base station 16 is releasably mounted to a mounting plate attached near monitor 138, through suitable mounting means. As illustrated in FIG. 10, base station 16 has a cavity 140 for storing electronic body unit 14, when electronic body unit 14 is not being used or is disconnected from the patient in other cases. In addition, base station 16 has a battery port 142 into which base station battery 144 is releasably inserted. Base station 16 can be constructed to have a plurality of battery ports that store and charge batteries when batteries are not in use. When base station 16 is not plugged into the AC power wall jack, base station battery 144 provides power to base station 16. When the base station 16 is operating from the AC wall plug, the base station 16 charges the base station battery 144, when the base station battery 144 is in the battery port 142. Base station 16 has a power switch 146 that turns on / off power to base station 16 and a power cord connection 148 to connect a power cord to the wall outlet for
ES 2 311 643 T3 AC power. The base station battery 144 is preferably a 3.6V lithium ion rechargeable battery. Consequently, the base station battery 144 and the electronic body unit battery 104 are preferably identical and interchangeable, so that each The battery can be used in either the body electronics unit 14 or the base station 16. The system is designed such that a discharged battery 104 from the body electronics unit can be exchanged with a charged battery 144 from the base station. In this way, a charged battery is always readily available for the electronic body unit. In addition, base station 16 has a lead switch 150 that allows the healthcare professional to instruct base station 16 to operate in either the "7-lead" mode or the "12-lead" mode.
As shown in FIG. 11, base station 16 has a user interface 152 that provides information to the healthcare professional or patient pertaining to the system's operating status or functionality. For example, user interface 152 can provide information on whether body electronics 14 is communicating or transmitting normally to base station 16, whether base station battery 144 is charging, or battery 144 is low, whether the battery 104 of the electronic body unit is low, or the power of the base station 16 is on, whether the base station 16 is malfunctioning or requires some other service. In addition, user interface 102 can provide instructions on the correct order or procedure for pairing or docking electronic body unit 14 with base station 16. Such information can be communicated to the healthcare professional or patient through user interface 152 in various ways, for example with a set of LEDs, LCD, text, audible tones, etc. An exemplary embodiment of the user interface 102 is illustrated in FIG. 11a.
In addition, the base station has a self-test function that monitors the integrity of the main functions, including the microprocessor, data acquisition, internal voltage references, and radio functionality. In the event that a fault is detected, the body electronics unit will capture the fault condition, stop data acquisition and transmission, and indicate that a fault has occurred via the conductor disconnected alarm.
A receiver 154, located within base station 16, receives signals sent to base station 16 from body electronics unit 14. As illustrated in Figure 12, receiver 154 includes a radio 156, a controller 158, an analog-to-digital converter (DAC) 160, a de-multiplexer 162, a transceiver 164, and a plurality of electrode signal channels 166. . Radio 156 demodulates received signals to identify data that represents the combined signals from the electrodes. In an exemplary embodiment, radio 156 includes a modulator for transmitting control information. The controller 158 controls the operation of the various components and can also process the signals from the radio 156, for example by interpolating data, converting the signals into digital information, generating control signals for the transmitter 108 in the electronic unit 14, operating any user input or output device, and diagnosing the operation of the ECG system. Preferably, controller 118 interpolates the signals from the electrodes to return the effective sampling rate to the 3 kHz or other frequency. This allows the reconstruction filters to have a cutoff frequency that is many times the bandwidth of the electrode signals, thus minimizing any difference in group delay at the frequencies of interest, i.e., less than 150 Hz. The DAC 160 converts digital signals to analog signals. De-multiplexer 162 separates the individually regenerated electrode signals into independent electrode signal channels 166. Transceiver 164 operates in accordance with the Bluetooth specification for two-way communication with transmitter 108.
Receiver 154 has nine electrode signal channels 166, corresponding to the 10 electrodes connected to chest assembly 12 and precordial assembly 60. Electrode signal channels 166 each comprise a sample and hold circuit 168 , a filter 170, and an attenuator 172. The sample and hold circuit 168 is controlled by the controller 118 so that the converted electrode signals appear simultaneously on each electrode signal channel 166. Other embodiments may include individual DACs that provide the signal substantially simultaneously. Filter 170 comprises a low pass reconstruction filter to remove high frequency signals associated with the DAC conversion process. The attenuator 172 comprises an amplifier to decrease the amplitude to a level associated with signals at the electrodes, which were previously amplified in the amplifiers of the body electronics unit 14. This results in a unity gain of the system, so that it does not introduce an error between the electrodes and the conventional ECG monitor.
The base station 16 transmits the ECG signals to the ECG monitor 138 via pre-existing or conventional monitor cables 174. In turn, the information is presented on the ECG monitor and reviewed by a physician. As shown in FIG. 13, the monitor cables 174 are releasably inserted into the snap terminals 176 located in the base station 16. Preferably, base station 16 has ten snap-in terminals 176 disposed on the left and right side of base station 16. Snap-in terminals 176 and monitor wires 174 are preferably labeled and color-coded, such that wires 174 of the monitor are properly connected to the base station 16. For example, the five snap-in terminals 176 located on the left side of base station 16 and monitor cable 174 can be labeled RL, LA, LL, RA, and V / V1. Additionally, the five snap-in terminals 176 on the right side of base station 16 and monitor cable 174 can be labeled V2, V3, V4, V5, and V6. When the ECG system is operating in the "7-lead" mode (ie, only the chest assembly 12 is used) the monitor cable 174 is plugged into the five push-in terminals 176 on the left side of the base station 16. When the ECG system is operating in the “12
ES 2 311 643 T3 conductors ”(ie using chest assembly 12 and precordial assembly 60) both monitor cables 174 plug into terminals 176 snap, the four terminals 176 snap on the left side of the base station 16 will be used for the chest assembly electrodes and the remaining six snap-on terminals 176 will be used for the precordial assembly electrodes.
There may be cases where there will not be a base station 16 in every ward or hospital room to be used with the body's electronic unit 14. In such cases, an adapter assembly 178 can be used to connect the chest assembly 12 or the precordial assembly 60 to the ECG monitor 138. In an exemplary embodiment, adapter assembly 178 allows chest assembly 12 or precordial assembly 60 to be plugged directly into a conventional or existing telemetry transmitter. FIG. 14 depicts an adapter assembly 178 having an assembly receptacle 180 that connects to chest assembly 12 or precordial assembly 60, and a telemetry box receptacle 182 that connects to a conventional or existing telemetry transmitter. In another exemplary embodiment, adapter assembly 178 allows chest assembly 12 or precordial assembly 60 to be plugged directly into existing ECG monitor link cables. Figure 15 depicts an adapter assembly 178 having an assembly receptacle 184 for connecting to chest assembly 12 or precordial assembly 60, and a cable assembly 185 for connecting to conventional or existing ECG monitor link cables. Cable assembly 185 has a cable 186 that connects to a link cable adapter 188 to connect to an ECG monitor link cable. In another exemplary embodiment, adapter assembly 178 allows chest assembly 12 or precordial assembly 60 to be plugged directly into standard lead wires that connect to an ECG monitor. Figure 16 depicts adapter 178 with a set receptacle 190 for connection to chest set 12 or chest set 60 and a lead wire set 192 for connection to a lead set. Cable assembly 192 has a cable 194 that connects to a lead wire adapter 196 to connect to standard lead wires. Various configurations of adapter 178 are possible, depending on the standard lead wire connector configuration.
Figure 17 depicts the method for monitoring cardiac activity in the patient's heart, using the wireless ECG system of the present invention. In step 198, the electrodes are placed on the body of the patient. In step 200, the chest assembly 12 and / or the precordial assembly 60 is positioned on the body of the patient, connecting the electrode connectors 21, 62 to the electrodes. In step 202, the chest assembly 12 and / or the precordial assembly 60 are plugged into the body electronics unit 14. In step 204, electronic unit 14 and base station 16 are paired by inserting tab key 132 into base station 16, tab key 132 is removed from base station 16, tab key 132 is inserted into unit electronics 14 from the body, token key 132 is removed from electronic unit 14, and token key 132 is reinserted into base station 16. Alternatively, docking can be achieved by inserting token key 132 into body electronics unit 14, token key 132 is removed from body electronics unit, token key 132 is inserted into base station 16, token key is removed 132 from the base station 16, and the token key 132 is reinserted into the electronic unit 14 of the body. In step 206, electrical signals from the patient's heart are detected, and transmitted to body electronics unit 14 through chest assembly 12 and precordial assembly 60. In step 208, electrical signals from the heart are transformed by the electronic unit 14 of the body, from analog signals into digital signals. In step 210, the body electronics unit 14 transmits the digital signals to the base station 16, via radio transmission. In step 212, the base station 16 transforms the digital signals into analog signals. In step 214, the base station 16 transmits the analog signals to the ECG monitor 138, via the monitor leads 174. At step 216, the ECG monitor 138 processes the analog signals into useful information that can be displayed on the monitor 138. In the above specification, the present invention has been described with reference to specific embodiments thereof. It will be apparent to those skilled in the art that a person understanding this invention can devise changes or other embodiments or variations, utilizing the principles of this invention, without departing from the broad scope and scope of the invention. The specification and drawings are therefore to be considered illustrative rather than restrictive. Consequently, the invention is not intended to be limited, except as may be necessary in light of the appended claims.
Contents4
13 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
73 members in 13 offices
Priority claims5
| Document | Office | Kind | Date |
|---|---|---|---|
| 20010998733 | United States of America | – | |
| 99873301 | United States of America | A | |
| 99873301 | United States of America | A | |
| 02794057998733 | – | – | – |
| US20010998733 | – | – | – |
Members73
| Document | Office | Kind | |
|---|---|---|---|
| CA2414309A1 | Canada | A1 | |
| WO0205700A2 | World Intellectual Property Organization (WIPO) | A2 | |
| AU7596501A | Australia | A | |
| WO0205700A3 | World Intellectual Property Organization (WIPO) | A3 | |
| US2002072682A1 | United States of America | A1 | |
| EP1303213A2 | European Patent Office (EPO) | A2 | |
| US2003105403A1 | United States of America | A1 | |
| CA2468530A1 | Canada | A1 | |
| WO03047427A2 | World Intellectual Property Organization (WIPO) | A2 | |
| AU2002359515A1 | Australia | A1 | |
| AU2002359515A2 | Australia | A2 | |
| MXPA03000499A | Mexico | A | |
| CA2470383A1 | Canada | A1 | |
| WO03061465A2 | World Intellectual Property Organization (WIPO) | A2 | |
| US6611705B2 | United States of America | B2 | |
| AU2003210609A2 | Australia | A2 | |
| US2003199777A1 | United States of America | A1 | |
| WO03061465A3 | World Intellectual Property Organization (WIPO) | A3 | |
| WO2004002301A2 | World Intellectual Property Organization (WIPO) | A2 | |
| AU2003280415A1 | Australia | A1 | |
| AU2003280415A8 | Australia | A8 | |
| WO2004002301A3 | World Intellectual Property Organization (WIPO) | A3 | |
| US2004073127A1 | United States of America | A1 | |
| JP2004512864A | Japan | A | |
| US2004127802A1 | United States of America | A1 | |
| NO20042460L | Norway | L | |
| KR20040081427A | Republic of Korea | A | |
| EP1467651A2 | European Patent Office (EPO) | A2 | |
| NO20043030L | Norway | L | |
| EP1478267A2 | European Patent Office (EPO) | A2 | |
| KR20040101210A | Republic of Korea | A | |
| WO03047427A8 | World Intellectual Property Organization (WIPO) | A8 | |
| MXPA04005165A | Mexico | A | |
| EP1519677A2 | European Patent Office (EPO) | A2 | |
| AU2001275965B2 | Australia | B2 | |
| MXPA04007038A | Mexico | A | |
| US2005177052A1 | United States of America | A1 | |
| MXPA04012556A | Mexico | A | |
| MXPA04012556A | Mexico | A | |
| JP2005532849A | Japan | A | |
| US2005251002A1 | United States of America | A1 | |
| US2005251003A1 | United States of America | A1 | |
| US2005251004A1 | United States of America | A1 | |
| IL162930A0 | Israel | A0 | |
| JP2006500964A | Japan | A | |
| JP2006501873A | Japan | A | |
| CA2414309C | Canada | C | |
| US7197357B2 | United States of America | B2 | |
| US7272428B2 | United States of America | B2 | |
| US2008009694A1 | United States of America | A1 | |
| EP1303213A4 | European Patent Office (EPO) | A4 | |
| US7403808B2 | United States of America | B2 | |
| EP1467651B1 | European Patent Office (EPO) | B1 | |
| AT412368T | Austria | T | |
| ATE412368T1 | Austria | T1 | |
| DE60229664D1 | Germany | D1 | |
| EP2008580A2 | European Patent Office (EPO) | A2 | |
| ES2311643T3This record | Spain | T3 | |
| JP2009183721A | Japan | A | |
| EP1519677B1 | European Patent Office (EPO) | B1 | |
| AT461656T | Austria | T | |
| ATE461656T1 | Austria | T1 | |
| DE60331833D1 | Germany | D1 | |
| EP1519677B9 | European Patent Office (EPO) | B9 | |
| US7860557B2 | United States of America | B2 | |
| US2011092835A1 | United States of America | A1 | |
| US7933642B2 | United States of America | B2 | |
| JP4699694B2 | Japan | B2 | |
| US2011160604A1 | United States of America | A1 | |
| US8255041B2 | United States of America | B2 | |
| EP2008580A3 | European Patent Office (EPO) | A3 | |
| EP2008580B1 | European Patent Office (EPO) | B1 | |
| ES2538680T3 | Spain | T3 |
Numbers
- Publication
- 2311643
- Publication, DOCDB
- 2311643
- Publication, EPODOC
- ES2311643T
- Application
- 2794057
- Application, DOCDB
- 02794057
- Application, EPODOC
- ES20020794057T
Titles2
- Spanish
- SISTEMA INALAMBRICO DE ELECTROCARDIOGRAFIA.
- English
- WIRELESS ELECTROCARDIOGRAPHY SYSTEM.
Classification
- CPC, 2
- A61B5/0006
- A61B5/282
- IPC, 3
- A61B5 0245
- A61B5 00
- A61B5 308