Apparatus for improved assisted ventilation

ES 2 805 083 T3

DESCRIPTION

Device to improve assisted ventilation

Background of the invention

Intubation is the placement of a tube from an intubation device into the airway lumen of a patient's body to provide assisted ventilation of the lungs to maintain a supply of oxygen to the blood in cases where the patient cannot breathe alone. Intubation in cases of respiratory distress involves placing a tube in the patient's windpipe. Tracheal intubation also involves placing an endotracheal tube into the patient's windpipe through the vocal cords, so the caregiver must also take care to avoid damaging the vocal cords. In many cases, care must be taken when intubating a patient, as improper tube placement can cause additional harm to the patient. For example, many conventional intubation devices rely on an inflatable cuff that forms a seal against the lumen wall to maintain a position of the tube within the lumen. Over-inflation of the cuff can cause internal bleeding in the patient. Another major problem is that great care must be taken to avoid placing the intubation tube into the esophagus instead of the trachea. In such cases, with conventional devices, the first aid professional or physician cannot adequately ventilate the patient and the patient may suffer further injury.

Even properly trained medical caregivers and first aid professionals should proceed with caution during intubation to avoid improper placement of the intubation device or to avoid unwanted insertion errors and risk of injury. Endotracheal tube delay and / or displacement, such as improper placement of the endotracheal tube in the esophagus, can potentially lead to neurological damage or death. The co location of inadequate endotracheal tube may also compromise the protection of the airways or cause inadequate ventilation. Therefore, it is imperative to intubate a patient quickly and place the endotracheal tube correctly when a medical condition arises.

To reduce the risk of complications during intubation, the caregiver, whether a first aid professional such as an emergency medical technician, a paramedic, or a nurse or physician, should proceed as quickly as possible but with caution to avoid possible complications. . In addition, a first aid professional must often attempt to intubate the patient in a highly inconvenient location such as a bathroom, restaurant, or other area not conducive to providing adequate medical care and treatment.

Assisted ventilation in cardiac arrest also requires the rapid and accurate placement of an intubation device within the trachea so that chest compressions can occur. In such cases, intubation allows ventilation of the lungs and a supply of oxygen to the blood, while chest compressions allow blood circulation.

American Heart Association protocols for cardiopulmonary resuscitation (CPR) previously required a pause every fifteen chest compressions to allow two ventilations. The 2010 American Heart Association protocols decreased the frequency of ventilations so that chest compressions are paused after every thirty compressions to allow two ventilations. The main reasons for the change in protocol are believed to be: 1) reducing the amount of intrathoracic pressure associated with positive pressure ventilations since positive pressure ventilations decrease the efficiency of the heart; and 2) minimize interruptions of chest compressions to maintain a constant blood pressure. Consequently, most caregivers currently only ventilate the patient simultaneously and provide compressions if the patient is adequately intubated.

Figure 1 provides a partial view of a patient's oral cavity 10, tongue 12, and pharynx 14 where pharynx 14 is the membrane-lined cavity at the back of oral cavity 10. Pharynx 14 includes openings of the esophagus 16 and the trachea 18. As shown, the openings to the esophagus 16 and the trachea 18 are adjacent to each other. When a medical caregiver attempts to intubate a patient, the caregiver will attempt to place the intubation device within the trachea 18 to provide oxygen to the lungs 2. As noted above, the caregiver should try to avoid placing the intubation device within of the esophagus 16 and in doing so you must often proceed slowly and with caution to avoid causing unwanted trauma to the vocal cords or other structures within the body.

The wall of the esophagus 16 is made up of smooth, striated muscle. Since the esophagus 16 relies on peristalsis to move food into the stomach, the walls of the esophagus 16 are naturally compatible and have no structural reinforcement. The trachea 18, on the other hand, is relatively stronger and is naturally designed not to collapse given its function of transporting air to the bronchi and lungs 2. The wall of the trachea 18 includes a series of cartilaginous semicircular rings 20 that prevent the trachea 18 from collapsing. Trachea 20 extends anteriorly to esophagus 16 where the openings of esophagus 16 and trachea are separated by a small flap, the epiglottis 22. The epiglottis 22 protects the trachea when the person ingests food or other substances.

ES 2 805 083 T3

Figure 2 illustrates a conventional device 50 used to intubate a patient. As shown, device 50 is inserted through the mouth and oral cavity into trachea 18. The caregiver should direct device 50 into trachea 18 instead of the esophagus while traversing the epiglottis 22 and vocal cords 24 The caregiver must take special care to avoid damaging the vocal cords. 24. Once properly positioned, the caregiver can optionally inflate 52 a balloon in device 50 to anchor the device within trachea 18. After the caregiver confirms placement of device 50, ventilation of the patient can take place.

Today, the Combitube, supplied by Nellcor, is commonly used for airway management. The Combitube, also known as a dual-lumen airway, is a blind insertion airway device (BIAD) used by first aid professionals as well as in an emergency room. The Combitube is designed to allow tracheal intubation of a patient with respiratory distress using a cuffed double lumen tube. The double lumen tube is inserted into the patient's airway to allow ventilation of the patient's lungs. Inflation of the cuff allows the device to function similar to an endotracheal tube and generally closes the esophagus, allowing ventilation and preventing pulmonary aspiration of gastric contents.

However, the placement of traditional intubation devices is very difficult due to the risk of incorrect device placement. The risk of a device being misplaced can be fatal if it is not recognized. The conventional devices described above require placement by a person who is well trained in the placement of such devices. Additionally, even well-trained individuals should proceed with caution when placing conventional devices.

In addition, there remains a need to improve the timing of air delivery during artificial ventilations of a patient. This need remains especially when the patient is experiencing distress and requires both ventilation for oxygen and chest compression to restore blood circulation. At present, if the act of artificially ventilating the person (for example, by assisted ventilation or mouth-to-mouth) and providing chest compressions is not timed, such as during normal CPR, the person's normal artificial ventilation can act in a short time. against the effectiveness of compression. For example, assisted ventilation by repeatedly delivering a large bolus of air can increase pressure within the chest cavity and increase resistance by increasing pressure on the heart. This back pressure can prevent the heart and lungs from filling with blood. As a result, impeding the ability of the heart and lungs to fill with blood makes chest compression less effective as a smaller volume of blood circulates after compression.

There remains a need for a ventilation device and / or system that can effectively ventilate people and can be positioned effectively with minimal training required by the caregiver. In addition, there remains a need for such ventilation devices and methods to optimize the effect of providing chest compression-assisted ventilation to circulate oxygenated blood within a person.

WO2011 / 154499 relates to a system for providing control signals for ventilation or compression, respectively. The system comprises a means for receiving information to receive, for resuscitation, information related to a compression parameter and / or ventilation parameter, based on a parameter indicative of blood circulation, a processing component to evaluate the different values ​​of the chest compression parameter and / or ventilation parameter based on the parameter indicative of blood circulation and obtain, on the basis of said information, a value for the ventilation parameter and / or the chest compression parameter respectively, and a control signal generator for generating control signals in accordance with the obtained ventilation parameter or the chest compression parameter.

Document US 2013/146051 discloses a system according to the preamble section of claim 1.

Summary of the invention

The invention is defined in the claims.

The present description includes devices and methods that allow for improved assisted ventilation of a patient. The methods and devices provide a number of benefits over conventional approaches to assisted ventilation. For example, the methods and devices described herein allow blind insertion of a device that can allow ventilation, regardless of whether the device is positioned within a trachea or esophagus. Some variations of devices and methods allow minimally trained observers and inexperienced individuals to place an advanced airway for assisted ventilation. The devices described herein can be designed such that a single size can accommodate a variety of sizes of patients, thus reducing the number of different size devices that need to be kept in inventory. Additionally, having devices that can accommodate a wide range of people reduces the need for a first aid professional to assess the anatomical features of a patient before acting on the patient. In patients with heart failure, giving large boluses of air during CPR may cause the patient to hyperventilate, which may decrease the effectiveness of the breath.

ES 2 805 083 T3

CPR. Elevated intrathoracic pressure can ultimately reduce the effectiveness of chest compressions. Current device and method variations allow controlled ventilation, preventing hyperventilation.

In another variation, the devices described in the present disclosure allow for improved assisted ventilation of a person. For example, a variation of the method includes inserting a ventilation device into the person by advancing an operating end of the ventilation device into a person's body passage where the operating end includes a distal opening fluidly coupled to a first lumen and an opening. medial fluidly coupled to second lumen; drawing the suction through the opening and attempting to maintain a vacuum through the first lumen and the far opening for a predetermined period of time; automatically ventilate the person through the second light upon sensing the vacuum for the predetermined period of time and holding the suction to maintain the vacuum; and automatically ventilating the person through the first light by not detecting the vacuum for the predetermined period of time; where the automatic ventilation of the person occurs at a predetermined time; measuring a condition of a chest cavity to determine a change in the chest cavity; and altering a moment of the person's automatic ventilation by detecting the change in the condition of the thoracic cavity.

The present disclosure also includes an artificial ventilation system of a person, the system comprising: a ventilation device configured for insertion into a breathing opening of the person and having an operative end to be positioned within a body passage of the person. , the ventilation device having a pressure sensor configured to detect pressure changes within the body duct; and the ventilation device having a control system configured to deliver an air bolus into a person's airway at a predetermined rate until detection of the pressure change within the body passage, where the control system is then configured to alter the predetermined rate by delaying the delivery of the air bolus until the sensor detects the pressure change in the air within the body duct, where the pressure change within the body duct is the consequence of chest compression.

Measurement of the condition of the thoracic cavity may include measurement of the condition of the thoracic cavity using the ventilation device or measurement of a change in compression of the chest of a patient. For example, measuring the change in compression of the patient's chest comprises observing a force applied to the ventilation device through the body passage. Alternatively, measuring the change in compression of the patient's chest comprises observing a deflection of the patient's chest using one or more sensors on the chest.

In a further variation, measuring the condition of the thoracic cavity comprises measuring a state of the air flow within the thoracic cavity. Said measurement can be performed using a sensor in the ventilation device and where measuring the state of the air flow within the thoracic cavity comprises detecting the air flow, pressure and / or volume using the sensor. Also, the sensor can monitor an air flow direction.

The timing of artificial ventilation can be altered by using the sensor to determine when a pressure in the body duct increases and by administering air to automatically ventilate the person when the pressure in the body duct increases, or at least before the decrease, The ventilations act as an internal chest compression, then the chest recoil draws air into the lungs.

The methods may further include providing feedback based on measurement of the condition of the chest cavity. Such feedback may include information related to compression, where the information is selected from phase, frequency, efficiency, depth, and timing. Feedback can also be based on measurement of the condition of the chest cavity, which comprises measuring the quality of chest compression by determining a change in a volume of air in the chest cavity. In some variation, the feedback comprises information to increase or decrease a compression applied to a patient's chest.

Variations of the method include altering the timing of ventilation to initiate automatic ventilation of the person when a pressure increases, decreases, or reaches a maximum pressure in the body passage. The method may further comprise continuing to measure the condition of the chest cavity to determine the change in the chest cavity after altering the time of automatic ventilation of the person and automatically re-ventilating the person at the predetermined time by not detecting the change. in the thoracic cavity.

In a further variation, the method may further include adjusting the ventilation device to suspend automatic ventilation of the person and manually ventilating the person while maintaining suction to maintain vacuum if vacuum is detected.

The methods described herein may include a mask that is slidably fitted along the ventilation device and where the mask can be pressed against the person with a manual actuator or actuator to isolate the person's breathing opening from a external atmosphere. Normally, the mask will not seal against the patient during automatic assisted ventilation. Therefore, during CPR, the system is open. Sealing the mask against the patient and initiating a manual override can shut down the system and deliver an air bolus to manually ventilate the patient.

ES 2 805 083 T3

The methods described herein may also include electrically stimulating a heart of the person using the ventilation device.

In another variation, the method of artificial ventilation of a person may comprise inserting a ventilation device into a breathing opening of the person and placing an operative end of the ventilation device within a body passage of the person, the ventilation device having a pressure sensor configured to detect pressure changes within the body passage; delivering a bolus of air into a person's airway at a predetermined rate; altering the predetermined rate by delaying the delivery of the air bolus when the sensor detects a pressure change in the air within the body duct, where the pressure change within the body duct is a consequence of chest compression.

The method may further comprise that the delivery of the air bolus into the person's airway occurs after a predetermined delay. In some variations, the sensor is configured to intermittently detect pressure changes within the body passage.

In another variation, the method further comprises, after altering the predetermined rate, the ventilator resuming the delivery of the air bolus at the predetermined rate if the pressure sensor cannot detect a pressure range within a first period of weather.

In another variation, the method of ventilating a person includes inserting a ventilation device into a breathing opening of the person and advancing an operating end of the ventilation device into a body passage of the person, where the operating end includes a first aperture fluidly coupled to a first lumen and a second aperture fluidly coupled to a second lumen, where the second opening is located along the venting device proximal to the first opening; suction through the first opening to induce collapse of the body passage and maintain suction for a period of time; monitoring a fluid parameter to determine if the body duct is collapsing; automatically ventilate the person through the second lumen upon detecting the collapse of the body passage and maintain suction to maintain the collapse of the body passage; and automatically ventilate the person through the first light by not detecting the collapse of the body passage; wherein the administration of an air bolus during automatic ventilation of the person occurs initially; measuring a condition of a chest cavity to determine a change in the chest cavity; and altering the timing of air bolus delivery during automatic ventilation of the person by detecting the change in the condition of the chest cavity.

In another variation, the present disclosure includes a method of artificially ventilating a person by attaching a ventilation device to a breathing opening of a breathing passage of the person; placing a pressure sensor in fluid communication with the airway, the pressure sensor configured to detect pressure changes within the airway; delivering a bolus of air into the person's airway at a predetermined rate; and altering the predetermined rate by delaying delivery of the air bolus until the sensor detects a pressure change in the air within the respiratory passage, where the pressure change within the respiratory passage is a consequence of chest compression. Said method can include any device, including conventional ventilation devices.

The present disclosure also includes a system for artificially ventilating a person using an oxygen source, the system comprising: a ventilation device having a pressure sensor configured to detect pressure changes within the body duct, the pressure sensor being positioned in a part of the device configured to be inserted in a body passage of the person; a command configured to deliver an air bolus into a person's airway at a predetermined rate, where the command is configured to monitor the pressure sensor and upon detecting a change in pressure, the command alters the predetermined rate by delaying delivery of the air bolus.

The present disclosure also includes devices for ventilating a person. In one example, said device comprises a tubular member having at least a first and second lumen, where the first lumen is fluidly coupled to a first opening distally of a medial opening, where the medial opening is fluidly coupled to the second lumen. , where the first opening and the medial opening are fluidly insulated within the tubular member; the tubular member being configured to measure a light condition of a body to determine a change in a thoracic cavity of the person; a control system having a suction source and a gas supply lumen, the control system having a valve configured to fluidly couple the gas supply lumen to either the first lumen or the second lumen; The control system is also capable of suction from the suction source through the first opening and the first light, where the control system is configured to monitor the first light for vacuum to indicate the collapse of the body passage and the formation of a seal at the first opening; wherein the control system is also configured to selectively form a ventilation path from the supply light to the first or second light by selecting the first light as the ventilation path if collapse of the body passage is not detected; and selecting the second light as the ventilation route if collapse of the body passage is detected; wherein the control system is configured to automatically ventilate the person through the ventilation path at a first frequency; and where the control system is also configured to alter the first frequency upon sensing the light condition of the body.

ES 2 805 083 T3

The system and methods described herein may be compatible with devices that monitor the concentration or partial pressure of carbon dioxide (CO2) in respiratory gases (capnography). These devices are primarily monitoring tools for use during anesthesia and intensive care monitoring expiratory CO2 that are of interest when using rebreathing systems. The ability to integrate the ventilation systems described herein with such capnography systems allows for better patient care. Additionally, the systems and methods described herein may be compatible with equipment found in emergency vehicles such as oxygen supplies and / or power supplies. In some variations, the system of the present disclosure may also provide audio or even video instructions (through the use of a screen) to ensure proper operation in those situations where the system may be used by non-first responders. are trained emergency personnel.

Brief description of the drawings

The invention is better understood from the following detailed description when read in conjunction with the accompanying drawings. It must be emphasized that, in accordance with common practice, the various features of the drawings are not to scale. Rather, the dimensions of the various features are arbitrarily enlarged or reduced for the sake of clarity. Also for clarity, certain features of the invention may not be represented in some of the drawings. The drawings include the following figures:

Figure 1 provides a partial view of a patient's oral cavity, tongue, pharynx, as well as esophagus and trachea.

Figure 2 illustrates an example of a conventional device used to intubate a patient.

Figure 3 illustrates various components of an example of an improved ventilation system.

Figures 4A to 4C illustrate a partial sectional view of an operating end of an improved ventilation device.

Figures 5A to 5E show a representation of the ventilation process of a patient using an improved ventilation device.

Figures 6A through 6C show additional variations of an operating end of a ventilation device. Figure 7 illustrates a schematic of an electrically powered system.

Figure 8A shows an example of a component schematic for a pneumatically actuated system as described herein.

Figure 8B provides a list of components for the schematic of Figure 8A.

Figure 8C shows a list of various modes for the system.

Figures 8D to 8M illustrate various flow paths for the various modes of operation.

Figure 9A illustrates another variation of a device useful for providing assisted ventilation with improved results by monitoring a chest cavity condition.

Figures 9B to 9C show a partial isometric view and partial cross-sectional views of the mask and actuator used to close the system and initiate manual ventilation.

Figures 10A and 10B illustrate examples of the operating end of the device when inserted into a human body lumen and monitoring a chest cavity condition.

Figures 11A and 11B illustrate a variation of a system for artificially ventilating a person using an oxygen source, such as those described herein.

Figure 11C shows an external device that is used to control the ventilator described herein.

Figure 12 provides a schematic of a control system that relies on gas supply to provide a source of both ventilation and suction.

Figures 13-22 illustrate an example of circuitry for sensing the phase, frequency, depth, and effectiveness of a chest compression with a resistance located on an airway tube located in the patient's mouth, trachea, or esophagus.

Detailed description of the invention

Before describing the devices, systems, and methods of the present invention, it will be understood that this invention is not limited to particular therapeutic applications and that the implant sites described, as such, may vary. It should also be understood that the terminology used herein is only for the purpose of describing particular embodiments and is not intended to be limiting, as the scope of the present invention will be limited only by the appended claims.

Unless otherwise defined, all technical and / or scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the present invention belongs. The terms proximal, distal, near and far when used indicate positions or locations relative to the user where proximal refers to a position or location closer to the user and distal refers to a position or location further from the user.

ES 2 805 083 T3

Figure 3 illustrates various components of an example of an improved system in accordance with the present disclosure. As shown, the ventilation device 100 includes an operating end 102 that is inserted into a patient. The operating end may include a distal tube 104 that contains a first lumen (not shown), which extends through a distal opening 106 of the ventilation device 100 and is in fluid communication with a control unit (also called a ventilator) 150. and / or supply source 160 through one or more proximal tubes 118. Control unit 150 may also include apparatus designed to provide suction, as well as a collection container. In operation, control unit 150 directs suction or applies a vacuum through a first fluid path 122, which in turn causes suction or negative pressure at distal opening 106. Source 160 may comprise oxygen, air, or any other gas that is desired for administration ventilation into the lungs. Font 160 can be nested within the physical construct of command 150. However, source 160 may be optional for the command to ventilate the patient using only ambient air.

Control unit 150 maintains device 100 in this state for a set period of time and monitors the pressure parameters or flow parameters within the first lumen to determine whether to vent through the first or second lumen. The example illustrated in Figure 3 also includes a connector 108 with one or more features that aid in the correct operation of the device. These features are described in detail below. Additionally, the distal opening 106 may include any number of holes in the distal end of the device as long as the holes are in a fluid path with the first lumen. Similarly, medial aperture 112 may comprise any number of apertures as long as said apertures are in fluid communication with the second lumen. Additionally, variations of the device can also be inserted through a nasal opening instead of a mouth.

Ventilation device 100 further includes a proximal tube 110 that houses a second lumen (not shown) that exits device 100 at a medial opening 112. As discussed below, the distal opening and the first lumen are fluidly isolated from the opening. medial and second lumen through the operating end of device 102 to control unit 150. This fluid isolation allows control unit 150 to determine which light to use to ventilate the patient. The control unit directs flow through a second fluid path 124 that is fluidly coupled to the second lumen and medial opening 112 when the device is positioned in esophagus 16 instead of trachea 18.

The ventilation system 100 illustrated in Figure 3 also shows an optional mask 114 with optional ventilation holes 116. Variations of the system may include alternative configurations without a mask or with other devices such as a mouth guard or any other mounting device. Common use. As discussed below, mask 114 or other mounting apparatus can be used to assist the caregiver in correctly orienting device 100 as it is inserted into the patient. Variations of the device can include a balloon, sponge, or any other structure that secures the proximal region of the device to the patient to ensure that gas is directed to the lungs during inhalation. The mask (or other structure described herein) may include a security band, strip of tape, or temporary adhesive to secure the mask in place on the patient. The mask or similar feature can be used to determine how far to advance the operating end 102 into the patient. Alternatively or in combination, device 100 may include graduated markings 134 to assist the caregiver in correctly advancing the device into the patient. The mask can be slidable to adjust the length from the mask to the distal or proximal opening.

Figure 3 also shows a representative figure of a control system 150 with a number of controls 152 that allow various operating sequences of the device, manual controls, or device overrides. For example, system 150 may include manual ventilation controls so that the caregiver can manually adjust the patient's inspiration and expiration. Controls 152 may include a reset or rapid ventilation mode to perform cardiopulmonary resuscitation. Controls 150 include a continuous air flow or continuous vacuum mode that can help remove debris or body fluids from the body passages. The controls also allow caregivers to connect device 100 directly to an endotracheal tube if the caregiver decides to intubate. In a further variation, the system can allow active ventilation consisting of blowing for a period and then sucking for a period through the active light in order to increase the efficiency of ventilation. In some variations, the system is configured so that the vents as well as other openings in the tube do not rotate relative to the mask so that the caregiver can align the openings with the trachea.

The device shown in Figure 3 may also include one or more electrodes located at the operating end. For example, connector 108 can act as an electrode and apply electricity to the heart in order to defibrillate a patient out of an irregular rhythm or increase heart rate or contractility. Additionally, one or more electrodes can be inserted or integrated into a tube designed to be placed in the mouth, esophagus, or trachea of ​​the patient. Such placement will be beneficial in that it would allow the manipulator a more direct path of electrical stimulation of the heart compared to the current use of pads placed on the patient's chest. A tube placed in the esophagus may detect a pulse more easily because the main arteries run parallel to the esophagus. This would allow rescuers to determine a pulse without having to touch the patient. It would also allow an untrained observer to administer CPR who was not trained to check the pulse. In addition, pressure sensors, as described below, can be placed on the tube that had been advanced into the patient's mouth that may be pressing on major arteries and could detect if there was a change.

ES 2 805 083 T3 pressure.

In further variations, the control system 150 can be integrated into one or more body parts of the device 102 rather than being a separate box-type configuration. In addition, the ventilation system 100 can optionally be configured to operate with a defibrillator. Alternative variations of the system 100 can be configured to provide an auditory, visual, or tactile sensation to indicate when a caregiver should deliver chest compressions.

Figure 3 also shows the depicted variation of device 100 having an optional balloon 132 or other expandable member located at an operating end. When used, the balloon can be positioned anywhere in the device adjacent to the distal opening 106. Alternatively or in combination, an adjacent balloon can be positioned adjacent to the medial opening.

The various tubes that make up the device 100 must be flexible enough to be able to navigate the device through the upper respiratory system. Alternatively or additionally, parts of the tube can be constructed to withstand being collapsed by the patient's mouth or teeth. In further variations the system 100 can be designed so that the distance between the distal opening 106 is adjustable relative to the medial opening 112 and / or the mask 114 (or even movable relative to the gradations 134). A similar variation includes a medial opening 112 that can be adjustably positioned relative to distal opening 106, mask 114, and / or gradations 134.

Figures 4A through 4C illustrate a partial sectional view of an airway unit or operating end 102 of a ventilation device 100 as described herein.

Figure 4A illustrates a first lumen 128 that is fluidly coupled to a distal aperture 106 and a second lumen 130 that is fluidly coupled to medial aperture 112 where the first and second lumens 128 and 130 are fluidly insulated from each other as described above. . Figure 4A also illustrates that the space 126 between the distal opening 106 and the medial opening 112 can be selected based on the intended patient. For example, since medial opening 112 is intended to be positioned in or around the pharynx when distal opening 106 is positioned in the esophagus or trachea, space 126 can be selected for a person of average build. In most cases, the operating end 102 of the ventilation device 100 will comprise a single-use disposable component. Accordingly, the ventilation device 100 can include a series of disposable components with different spacing 126 between the medial 112 and distal 106 openings. For example, the variable spacing can accommodate infants, children, minors, as well as various body sizes.

Figure 4B illustrates a partial cross-sectional view of the operating end 102 of the vent device of Figure 4A. Once the device is properly positioned within the patient, the control unit 150 applies a suction or vacuum through a first fluid path 122, then through the first lumen 128, and finally causes a vacuum in distal opening 106 as indicated by arrows 30. In further variations, the handler or caregiver may choose to remove food or other debris from the patient by delivering air through the first lumen 128 or attempting to use suction at the distal opening to remove particles or other bodily fluids. System 150 will continue to exert a vacuum through first lumen 130 for a period of time. If device 100 is correctly positioned within the trachea (as discussed below), system 150 will begin to ventilate through first lumen 128. In other words, system 100 will begin to cyclically deliver oxygen or other gas from source 160 and will remove carbon dioxide from the patient to properly ventilate the patient's lungs. In this situation, no flow is required through the second lumen 130 and the medial opening 112. Although Figure 4B shows the first light 128 to be located within the second light 130, any number of variations can be used. For example, the lights can be concentric or parallel. Additional variations even allow the lumens to be in fluid communication where one or more valves determine whether ventilation occurs through the distal opening or through the medial opening. The device can include any number of security checks to confirm that the location of the device does not change. For example, once the device confirms placement in the trachea, you can recheck to ensure that it is placed in the trachea for a predetermined interval. Alternatively, you can perform this verification on a sliding scale (for example, 1^to verification at 30 seconds, 2^to verification at 2 minutes, 3^to verification at 10 minutes, etc.). In a further variation, the system is designed to provide a safety check to ensure that the suction filter is not clogged causing an incorrect position reading. In such a case, the device provides ventilation out of the distal orifice once a vacuum is detected. This ventilation bolus can be small or large. By monitoring the vacuum and determining if it is lost during the distal air bolus, the device knows that the seal was in the esophagus and resumes distal suction and ventilation through the proximal ports. If vacuum is not lost during the distal air bolus, the device may assume that the filter is clogged and an error signal will indicate that the manipulator should replace the operating end of the device or monitor for clogs.

System 150 may comprise the mechanism that vents and produces suction or vacuum. In general, system 150 is reusable (as opposed to the generally disposable operating end). System 150 can be portable, attached to an ambulance or other emergency vehicle, or built within a cart or room. The

Variations include battery powered devices, pneumatically powered devices, or devices that require a power source (such as an AC outlet).

Figure 4C illustrates the condition where the distal opening 106 is located within the esophagus. In this situation, control unit 150 directs ventilation through second lumen 130. As shown by arrows 32, since medial lumen 112 is fluidly coupled to second lumen 130, ventilation 32 takes place at medial opening 112.

Figures 5A to 5E show a representation of the ventilation process of a patient using a ventilation device 100 as described herein.

Figure 5A illustrates the ventilation device 100 as a caregiver advances the device 100 into the oral cavity 10 over the tongue 12 and into the pharynx 14. At any time during the procedure, the caregiver can manipulate the device. manually to suck fluids, food particles, or other items from the body. As described herein, the caregiver can blindly advance the operating end 102 into the patient. As a result, the operating end 102 will terminate in the esophagus 16 or trachea 18 of the patient.

Figure 5B illustrates the condition in which the caregiver advances the operating end 102 into a trachea 18 of a person. Once the caregiver places the device 100, the caregiver can initiate the control unit 150 to begin the process for determining the placement of the device 100. Alternatively, one or more sensors on the device can automatically trigger activation of the unit. of control. In either case, the control unit draws a vacuum through distal opening 106 for a predetermined period of time. The vacuum reduces the pressure and draws air into the distal opening 106. The control unit 150 then evaluates a state of the device by monitoring the vacuum, air flow, or any other fluid parameter that would indicate whether the walls of the body duct, in this case the trachea 18, collapsed causing the formation of a vacuum seal. In those cases such as Figure 5B where the device is located within the trachea, the suction 30 will have little effect on the walls of the trachea 18. As previously indicated, the walls of the trachea 18 are reinforced with rings of cartilage 20 that provide structural rigidity of the airway. Since command 150 will not detect the formation of a vacuum seal at distal opening 106 (or within the first lumen) the system registers distal opening 166 as correctly located in trachea 18 (instead of esophagus 16) and, after a predetermined period of time (for example 10-15 seconds), command 150 stops drawing a vacuum and begins to ventilate the patient's lungs alternating between delivering gas from gas supply 160 and removing carbon dioxide. As a result, the first light is used as a ventilation light. It will be important for command 150 to differentiate changes in vacuum or flow that are a consequence of fluid or debris suction. In some variations of the device, the command 150 is configured to identify the formation of a seal when the vacuum is created or the flow drops to a degree sufficient that the device has formed a vacuum seal in place of suctioned fluids or a substance .

Control unit 150 can determine whether or not a seal is formed by measuring the voltage on a suction motor (or similar apparatus such as a venturi device that produces a vacuum) that causes negative pressure within the main lumen for suction. If the control unit 150 observes zero or minimum voltage on the suction motor after a predetermined time, then the control unit 150 will use the first light as the ventilation light.

Figure 5D illustrates a state where the caregiver advances an operating end 102 of the ventilation device 100 into an esophagus 16 instead of the trachea 18. Similar to the state depicted by Figure 5B above, once the caregiver places device 100, the caregiver can initiate control unit 150 to begin the process for determining the placement of device 100. As indicated above, additional variations of the device and the system may include one or more sensors that can automatically trigger the activation of the control unit.

Figure 5D depicts the state where the control unit 150 exerts a vacuum through the distal opening 106 for a predetermined period of time. The vacuum reduces the pressure and draws air into the distal opening 106. The control unit 150 then evaluates a state of the device by monitoring the vacuum, air flow, or any other fluid parameter that would indicate whether the walls of the body duct, in this case the esophagus 16 collapsed. As shown, the walls partially or fully collapse, resulting in the formation of a vacuum seal at the distal opening. 16. As noted above, the muscles form the walls of the esophagus 16. There is no reinforcing structure in the esophagus as opposed to the cartilage rings in the trachea 18. The control unit can be configured to monitor the formation of a vacuum seal and if the seal remains for a predetermined period of time, the control unit 150 directs ventilation 40 in and out of the medial opening 112 as depicted in FIG. 5E. As shown and discussed above, the space between the distal opening 106 and medial opening 112 can be selected so that the medial opening remains within or near the pharynx 14. However, variations of the device allow the medial opening to enter esophagus 16 as long as the opening 112 can continue to ventilate the patient.

Since the control unit 150 will not detect the formation of a vacuum seal at the distal opening 106 (or within the first lumen) the system registers the distal opening 106 as correctly located in the trachea 18 (instead of the

ES 2 805 083 T3 esophagus 16) and, after a predetermined period of time, the control unit 150 stops drawing a vacuum and begins to ventilate the patient's lungs alternating between administering gas from gas supply 160 and removing dioxide carbon. In this situation, the device uses the second light as the ventilation light. An additional benefit of locating the operating end 102 of device 100 within esophagus 16 is that the vacuum seal produces an anchoring effect that holds the device in position. This feature eliminates the need to secure the mask or other feature around the patient's head, neck, or face. In addition, if a caregiver accidentally pulls on device 100 while a seal is being formed, the vacuum seal simply breaks and the device is released from the esophagus 16. This provides a safety improvement over conventional ventilation devices that rely on a expandable balloon, which, when pulled, can cause trauma to the patient's airways, vocal cords, or other structures.

In certain variations, device 100 should stop ventilating after a period of time and produce suction through the distal opening. This stage is considered a safety feature in case the operating end is moved, relocated, etc.

Figures 6A through 6C show variations of the operating end 102 of a vent device as described herein. Figure 6A illustrates a connector having an opening 106 that is surrounded by a contoured surface. The contoured surface can help reduce the possibility of distal opening 106 clogging due to food particles or other fluids. This feature also helps reduce instances where the control unit misread an opening 106 that is clogged (with food particles or other body fluids) for an opening that formed a seal with the walls of the esophagus. Figures 6B and 6C illustrate additional variations of an operating end 102 of a ventilation device. In these variations, the operating end 102 can be manufactured with or without a connector. Figure 6B illustrates a straight tube having a plurality of openings 106. Figure 6C illustrates a beveled end having an opening 106.

As noted above, the device described herein can be pneumatically actuated using compressed gas and valves or electrically controlled. Figure 7 illustrates a schematic of an electrically powered device that uses a suction motor, air compressor, and circuitry to switch between a first fluid path 122 (ultimately fluidly coupled to a distal opening) and a second fluid path 124 ( finally fluidly coupled to a medial opening).

Figure 8A shows an example of a component schematic for a system as described herein that is pneumatically actuated. Figure 8B provides a list of the components found in Figure 8A. The valves operate in multiple states based on the conditions discussed above. The following description illustrates an example of the different states of the components found in the component schematic of Figure 8A.

Medial supply valve P1 (4/2);

State 1 (nominal, spring return): Controls the 15 second timing of vacuum delivery through the P2 Distal Delivery Valve;

State 2 (Powered): Provides supply for medial ventilation;

Pilot drive: 10 Hg vacuum

Distal Delivery Valve P2 (4/2)

State 1 (nominal, spring return): Provides supply for the Vacuum Generator;

State 2 (Powered): Provides supply for distal ventilation;

Pilot actuation: 40 psi from the flow controlled outlet of the Medial Supply Valve, State 1.

P3 pulse valve (3/2 normally open);

State 1 (nominal, spring return): Fill the Accumulator Volume at flow controlled frequency until the pressure set in the In-line Relief Valve is reached;

State 2: (actuated): Discharges volume from the accumulator to the Ventilation selector valve through a rapid exhaust;

Pilot actuation: 5 psi from outlet of in-line dump valve

P4 vent selector valve (3/2 fully transferred);

State 1 (nominal, spring return): Directs the Pulse Valve outlet to the Medial Ventilation Outlet;

State 2: (actuated): Directs the Pulse Valve outlet to the Distal Ventilation Outlet;

Pilot actuation: 40 psi from the outlet of the distal Delivery Valve, State 2

Operation valve M1 (Manual lever, 3 positions, All stopped);

ES 2 805 083 T3

State 1 (lever down, ON): Provides supply for the Medial Delivery Valve and the Distal Delivery Valve;

State 2 (lever centered, OFF / RESET): Blocks the supply, vents the system;

State 3 (lever up, VACUUM): Bypass all valves, provide supply to Vacuum Generator.

M2 mode valve (Hand lever, 3 positions, Stop / Stop / Momentary);

State 1 (Lever Down, Stop, VENTILATE): Provides supply for Pulse Valve and Vent Selector Valve;

State 2 (lever centered, stop, AVOID): Blocks supply to Pulse Valve and Ventilation Selector Valve.

State 3 (lever up, momentary spring return, ON DEMAND): Blocks supply to Pulse Valve, provides continuous flow controlled supply to Ventilation Selector Valve

The system illustrated by the component schematic of Figure 8A can have a variety of modes of operation. In one example, as shown in Figure 8C, the system may include 8 different modes of operations controlled by the position of various valves and the state of operation of a medial delivery valve.

Mode 0, where the system is set to a Shutdown position.

M1 set to OFF;

Main supply blocked; ventilated system;

Figure 8D shows Mode 1, where there is a continuous vacuum applied through the system.

M1 set to VACUUM

Ventilation system avoided; vacuum at the vacuum outlet; Vacuum indicator on

Figure 8E shows Mode 2, where the system participates in location detection;

M1 set to ON;

Aspirate in the vacuum outlet until the P2 pilot is activated (15s); Vacuum indicator on;

In Mode 3, the system participates in ventilation through the distal opening.

M1 set to ON; M2 set to VENTILATE;

No vacuum is detected; Pilot P2 activated; Pilot P4 activated.

Figure 8F shows mode 3A, where an accumulator fills at a controlled rate (0.67 s) until the Inline Flush Valve is activated (30 psi);

Distal ventilation indicator on.

Figure 8G shows Mode 3B: Pilot P3 is activated, closing P3 and letting Accumulator Volume escape through Quick Exhaust to P4; Distal ventilation indicator on. Mode 4 - Medial ventilation

M1 set to ON; M2 set to VENTILATE

Void detected; Pilot P1 activated; vacuum at the vacuum outlet.

Figure 8H shows Mode 4A where the accumulator is filled at a controlled rate (0.67 s) until the Inline Flush Valve is activated (30 psi);

Vacuum indicator on;

Medial ventilation indicator on.

Figure 8I shows Mode 4B: Pilot P3 is activated, closing P3 and letting Accumulator Volume escape through Quick Exhaust to P4;

Vacuum indicator on; Medial ventilation indicator on.

Figure 8J shows the 5-Prevent Vent (distal) mode;

M1 set to ON; M2 set to AVOID;

No vacuum is detected; Pilot P2 activated; Pilot P4 activated; supply to P3 and P4 blocked; Distal ventilation indicator on.

Figure 8K shows Mode 6 - Demand Ventilation (distal);

M1 set to ON; M2 set to ON DEMAND;

No vacuum is detected; Pilot P2 activated; Pilot P4 activated; supply to P3 blocked; continuous flow-flow regulated at P4; Distal ventilation indicator on

Figure 8L shows the 7-Avoid ventilation (medial) mode;

M1 set to ON; M2 set to AVOID;

Void detected; Pilot P1 activated; vacuum at the vacuum outlet;

supply to P3 blocked;

ES 2 805 083 T3

Vacuum indicator on;

Medial ventilation indicator on

Figure 8M shows Mode 8 - Ventilation on demand (Medial);

M1 set to ON; M2 set to ON DEMAND;

Void detected; Pilot P1 activated; vacuum at the vacuum outlet;

supply to P3 blocked;

continuous flow-flow regulated at P4; Vacuum indicator on; Medial ventilation indicator on.

Figure 9A illustrates another variation of a device useful for providing assisted ventilation with better results. The features and appearance of the illustrated example can be combined with any of the variations of the devices described herein. Also, features of the devices described herein that enhance the effectiveness of assisted ventilation can be used with conventional assisted ventilation devices.

As illustrated, the assisted ventilation device 100 includes an operating end 102 that is inserted into a patient. The operating end may include a distal tube 104 that contains a first lumen (not shown), which extends through a distal opening 106 of the ventilation device 100 and is in fluid communication with a control unit (also called a ventilator) 150. and / or supply source 160 through one or more proximal tubes 118. Control unit 150 may also include apparatus designed to provide suction, as well as a collection container (not shown). As noted above, device 100 may optionally include an improved control unit 150 that directs suction or applies a vacuum through a first fluid path 122, which in turn causes negative suction or pressure in the distal opening 106. Source 160 may comprise oxygen, air, or any other gas that is desired for administration ventilation into the lungs. Source 160 can be nested within the physical construction of command 150. However, source 160 may be optional for the command to ventilate the patient using only ambient air. Figure 9A also illustrates device 100 including features that allow assisted ventilation device 100 to deliver ventilation in a manner that improves the efficiency of the assisted ventilation procedure.

For example, the improved device 100 can include one or more structures used to determine a change in the chest cavity. Such changes may include physical movement of tissues within the chest cavity, force applied to operating end 102 of device 100, and / or deflection of any part of device 100. Alternatively or in combination, a change in the thoracic cavity may comprise a change in the fluid environment of the thoracic cavity, including any body passages that are in fluid communication with the thoracic cavity, eg, the airways, the esophagus, etc. .

Figure 9A illustrates the device 100 being capable of measuring parameters of the fluid in the chest cavity by means of a sensor 180 located along a portion of the operating end 102 of the device. Although sensor 180 is illustrated on proximal tube 110, sensor 180 can be positioned along any part of device 100 that allows monitoring of fluid parameters of the thoracic cavity and / or the body duct in fluid communication with the body. thoracic cavity. For example, device 100 may include one or more sensors 180 positioned along distal tube 104 and / or connector 108. Also, variations of the device include one or more sensors positioned within device 100.

Sensor 180 may comprise a pressure sensor, a fluid sensor, a transducer, or the like. Alternatively, in further variations, sensor 180 may comprise a light or passage having an open end positioned as described above, where the light or passage extends through the device through a sensor tube 182 allowing that the actual fluid parameters are read by the actual sensor located within device 100, tube 118, and / or control unit 150.

The variation illustrated in Figure 9A also shows a sensor 180 that is not aligned with the proximal tube 110 of device 100. As shown, the measurement surface (for example, the actual sensor or the light from sensor 184 can be positioned accordingly. so that tissue adjacent to device 100 does not obscure or affect sensor readings, however, additional variations of device 100 include sensors that are aligned with the body of the device. In addition, pressure from device 100 (eg, proximal tube 118) can be used to deliver air to sensor 180 by reducing obstructions that interfere with the measurement of any fluid parameters in the body lumen.

Figure 9A also illustrates a force sensing component, such as a strain gauge, fiber optic, transducer, or similar force / motion sensing structure that can be found anywhere along the operating end 102 of device 100. Force sensing component 190 is shown to be on distal tube 104, however, one or more force sensing components 190 may be positioned along any part of the device as long as component 190 senses a force applied to the chest by means of a resultant force that is applied to the device through movement of the displaced tissue by assisted chest compression.

ES 2 805 083 T3

The presence of both sensor 180 and force sensing component 190 in a single device is for illustrative purposes only. Certain variations of the device can include any combination of force sensing component, sensor, or both.

Figure 9A also shows the device including a manual ventilation actuator 186. In operation, the medical caregiver may use the manual ventilation actuator 186 to manually deliver a bolus of air through the device 100. Alternatively or in combination, the actuator Manual ventilation 186 can activate sensor 180 or force sensing component 190 to deliver a bolus of air on demand. This feature may be useful if the caregiver has obtained a pulse and intends to administer assisted ventilation alone. Alternatively, the caregiver can use the manual vent actuator 186 to deliver a bolus of air through any part of the device in an attempt to clear bodily fluids that might otherwise obstruct the device. The manual ventilation actuator 186 can operate while the device performs automated assisted ventilation where a bolus of air is delivered over a specified period of time. Alternatively or in combination, manual ventilation actuator 186 may deliver a bolus of air when ventilation device 100 (or command 150) is placed in manual mode.

In certain variations of the device, upon initiation of the manual actuator 186, the device is programmed to maintain ventilation through the respective opening that was selected in the automatic mode. For example, if the device is placed in the esophagus and then switched to manual operation, the control system can maintain suction to ensure that the esophagus closes the distal opening and forms a vacuum for manual ventilation to continue automatically through the proximal or medial opening 112. Similarly, if the device is placed in the trachea, operating the device in manual mode will cause the bolus of air to be expelled from the distal opening of the device.

In one example, actuator 186 comprises a hollow button, attached to the device and in line with tubing that connects to sensor 180. When the button is pressed, it sends a bolus of air to sensor 180 that signals control system 150 to start assisted ventilation. The volume of air provided by the manual actuator 186 can be predetermined. Alternatively, air can be administered until the caregiver releases actuator 186 to stop ventilation. In addition, mounting the actuator 186 mounted on the mask 114 is beneficial in that it allows the caregiver to ensure that the mask 114 is sealed against the patient's face with one or two hands while managing the on-demand ventilations.

Manual actuator 186 may also operate with one or more one-way valves (eg, a flap that allows air to escape when actuator 186 is not depressed). This ensures that there is no excessive pressure build-up in the airways and prevents barotrauma. This also allows for spontaneous breathing. When the ventilator is switched to demand ventilation mode, the lungs should only be isolated from the atmosphere during the inhalation period. This can be accomplished by having the demand ventilation actuator 186 mounted on a flap that is above an opening in the mask. The flap is designed to open when no pressure is being applied to the button, then once pressure is applied to the actuator, the flap seals against the opening, closing the system and allowing air to inflate the lungs. When the button to exhale is released, the flap pops out of the mask opening allowing air to escape and the lungs to deflate.

Figure 9B illustrates a variation of a portion of a device 100 showing a mask 14 having an actuator 186 that is coupled to an exhaust port 116. In this variation, the mask 114 also includes one or more pressure relief valves. 117 that will crack or allow flow beyond a set pressure. Said operational safety presents an unsafe pressurization of the airways by the device. Pressure release valves 117 may be surrounded by protrusions or features 115 that prevent objects from blocking valves 117. Device 100 is also shown with a fit control 183 that allows movement of mask 114 along the tube 110. Figure 8B also illustrates tube 185 that couples actuator 186 to light from sensor 184. As shown, the sensor light 184 can be coupled with a tee fitting or other fluid coupling so that a portion of the light is in fluid communication with the actuator 186 as described below.

Figure 9C illustrates a partial cross-sectional view of mask 114 and tube 110. As shown, when the mask is placed against the patient's breathing opening (ie, mouth or nose), air flow flows from the expiratory cycle. (represented by arrows 109) through a portion of the mask 114 and into a chamber 113 that is in fluid communication with the exhaust lights 117. However, in this condition, the actuator 186 is not being pressed against the mask 114 so that the exhaust port 116 remains open allowing air flow 109 to escape from the mask. Additionally, actuator 186 may be positioned on a shaft having a compressible air volume 111 that is in fluid communication with tube 185. Accordingly, although the mask 114 is pressed against the patient, the escape port 116 allows the system to be open (fluidly open).

Figure 9D illustrates a condition where the actuator is depressed or actuated (the actuator may be on a spring return or have elasticity to function as a spring return). Once actuated, the actuator 186 closes the system fluidly by closing the exhaust port 116. The action of the actuator 186 also

ES 2 805 083 T3 can be used to initiate a manual bolus of air through tube 110. For example, actuator 186 may have one or more electrical contacts or switches in region 111 that provide a signal to the control system to deliver an air bolus. In a further configuration, the actuation of the actuator 186 compresses the volume of air in the space 111 causing an increase in pressure P2 in the tube 185, which is coupled to the light of the sensor 184, this pressure increase causes the light of the sensor perform manual ventilation by delivering a bolus of air through tube 110. Likewise, when actuator 186 is released, the volume expansion of region 111 creates a pressure drop in tube 185 as well as in the lumen of sensor 184, where the sensor records the pressure drop to stop ventilation.

In addition to sensor 180 and / or sensor light 184, device 100 may include any number of additional lights to provide information to monitoring equipment. For example, the device may include one or more lights that can be fluidly coupled to a capnograph device. Alternatively or in combination, the sensor light 184 may also allow fluid coupling to a monitoring device. In such a case, the lights can be coupled to one or more openings (such as 180) located at the operating end of the device.

Figure 10A illustrates an example of the operating end 102 of device 100 when inserted into a human body lumen. In this example, the device is inserted into a trachea 18, where the device 100 detects that it is in an airway as described above. However, as shown in Figure 10B, variations of device 100 can also be placed in esophagus 16 using the process described above, temporarily sealing esophagus 16 to deliver air to respiratory passage 18.

In either case, device 100 is configured to begin assisted ventilation by delivering a bolus of air 40 at a predetermined rate. Device 100 is configured to measure a condition of a chest cavity to determine a change in the chest cavity, either by pressure within the chest cavity as indicated by PT or a force F applied to the chest by chest compressions. In the latter case, the force F applied to the chest causes movement of the tissue (such as the trachea or other tissue) which can be determined by a force sensing component 190 as discussed above. Detection of a change in the thoracic cavity by measuring a fluid characteristic, such as a change in PT pressure, is normally measured within a body passage (such as the trachea 18 or the esophagus 16). Such measurements can include measuring air flow, volume, pressure, etc.

In a variation, the initial or predetermined rate comprises 100 breaths per minute (ie, a bolus of air is delivered 100 times per minute). However, any frequency of administration is within the scope of this disclosure. Upon sensing a change in the condition of the chest cavity, typically due to chest compressions, the device 100 will adjust the timing and / or frequency of air delivery to achieve an optimal result. For example, the system can deliver an air bolus by detecting chest compression (either by force measurement or by fluid sensor measurement). In such a case, the air bolus increases the pressure in the chest cavity to act as an internal chest compression that compresses the heart and lungs from within, causing increased blood flow.

In device variations, the system monitors a change in a chest cavity condition continuously or with delay. In either case, the system can be configured not to respond to a change in chest cavity pressure driven by the delivery of the air bolus. For example, the system can ignore readings during and immediately after air bolus delivery.

The process of adjusting the delivery of an air bolus (either by timing and / or rate) in response to a particular phase of chest compression is intended for use during CPR. However, assisted ventilation can be achieved using a mechanical compression system or with a caregiver performing manual chest compressions.

The timing and / or rate alteration is designed to deliver a bolus of air with each compression or specific number of compressions and at a specific phase of compression of the patient's chest. As noted herein, ventilations are timed so that they both increase the efficiency of chest compression by increasing intrathoracic pressure during the downward movement of chest compression, which would increase pressure on the heart, thereby increasing blood flow. . During the upward motion of the compression, a portion of the ventilation could still be delivered to allow fresh air to enter the alveoli while allowing a portion of the upward motion of the compression to create a negative intrathoracic pressure that returns blood to the heart and draw air into the alveoli. This technique also prevents a rescuer from having to pause compressions to give ventilations, which decreases blood flow and reduces the patient's chances of survival.

When using the devices described herein, regardless of whether the device is placed in the trachea or esophagus, the airways are always open to the outside environment, greatly reducing, if not eliminating, the possibility of barotrauma. .

The data generated by the devices described in this document regarding compression efficiency

ES 2 805 083 T3 regarding depth, frequency, recoil time can be analyzed and presented by feedback to the caregiver in order to maximize the efficiency of compressions. All of this information will be used to increase the efficiency of compressions and thus increase the patient's blood flow and increase the patient's chances of survival. If a mechanical compression system is used, the cycle phase could be directly linked to device 100.

Additionally, the system can be configured to revert to a predetermined air bolus delivery rate, should chest compression stop / pause at any time. In such a case, the system can monitor the amount of time during which a change in the chest cavity is not detected. If no change is detected for a predetermined time, the control unit can reset the assisted ventilation rate to the initial rate or to an alternate rate that does not depend on chest compression. Also, if the patient's pulse is resumed, the system can continue to provide assisted ventilation at a rate, volume, etc. default. Alternatively, the system can introduce a manual mode where a caregiver can provide assisted ventilation on demand (eg, using the manual override button). Additionally, the system can be configured to monitor a patient's pulse and use pulse identification to adjust the rate of assisted ventilation or stop assisted ventilation.

The manual override allows the caregiver to deliver button-controlled on-demand ventilation that can be beneficial once the patient has regained a pulse, eliminating the need for external chest compression. As noted above, device 100 can still continue to isolate the lungs by collapsing the esophagus with suction and / or direct air through the appropriate lumen into the lungs, but change the ventilation to a bolus of delivered air. on demand of the caregiver. The manual override allows the caregiver to start the flow of air to the lungs. Release of the actuator stops air flow to the lungs to allow the patient to exhale. Alternatively, a single actuator actuation may supply a predetermined amount of air that ventilates the patient.

The system described herein can also be used with conventional rescue devices. For example, the ventilation system can be configured to work with an active chest compression device so that chest compressions and ventilations are timed to increase the effectiveness of both compression and ventilation. The coupling can be mechanical and / or electrical. The ventilation system may also include carbon dioxide sampling so that carbon dioxide levels are emitted through a signal or gas stream to a monitor or other means of notification as described herein.

Figures 11A and 11B illustrate a variation of a system for artificially ventilating a person using an oxygen source, such as that described herein. In the illustrated example, device 100 does not show for clarity in illustration how control system 150 can be used as a standalone unit having electrical control systems that have firmware that can be controlled through the system interface. 152, or it can be integrated or controlled with an external device (eg, a heart monitor, monitor / defibrillator, or other intensive care device). As shown, control unit 150 can be mounted on external device 162 and coupled to an oxygen source 160. As shown in Figure 11B, once coupled to external device 162, control unit 150 can be operated using built-in controls 152 or can be controlled via external device 162 via a wireless or wired connection. In such a case and as shown in Figure 11C, one or more of the integrated controls 152 of the control unit 150 may be displayed on the control / display 164 of the external device 162. The variation shown in Figure 11C illustrates controls for operate device 100 in a CPR mode, on-demand mode, or suction mode. However, any number of items can be displayed on the control / display 164 and / or on the built-in controls 152.

For example, device 100 can display information regarding phase, rate, efficiency, depth, chest compression ratios during CPR. Additionally, the device can display information to provide a manipulator with real-time feedback on the efficiency of assisted compressions through auditory or visual feedback, as well as information on whether to increase or decrease the speed of manual compressions, or whether to resume chest compressions. if pulses are missed or the caregiver stops chest compression too long.

Device 100 can also be configured with a rechargeable power source that can be charged when connected to an external device 162, or where the connection allows device 100 to be charged through a typical AC power source. In most cases, the control unit 150 will carry a power source capable of powering the device for a sufficient period of operation and a sufficient waiting period.

Figure 12 illustrates a further enhancement to increase the portability of the control unit 150. In this configuration, the control unit 150 relies on the oxygen source 160 to provide ventilation to the person, as well as to produce the vacuum described above. . Accordingly, to extend the oxygen source, the device may employ one or more vacuum valves 200, 202 that produce a vacuum as a result of the pressurized flow of oxygen where a vacuum valve operates at high flow to generate suction. Once a vacuum is established for a set period of time, the system can switch to a low flow vacuum valve 202 that generates high vacuum with low flow. Such a configuration increases the life of the oxygen supply.

ES 2 805 083 T3

In another variation, the devices described herein can be used to determine ventilation parameters using tubes that accommodate different sizes. For example, having a variety of different sized operating ends that were coordinated with a Broselow tape for pediatric applications. In this way, a caregiver could simply select the airway size recommended by Broselow tape and attach it to the ventilator. The caregiver would not have to adjust the ventilation parameters because the authentication process would indicate to the ventilator the approximate size of the patient based on the selected airway. Alternatively, the airway itself would reduce the volume, pressure, suction pressure that the patient received. An example of this method would be a narrowing of the vent tube that restricted flow so that the volume ventilated over a period of time would be less. Another example would be an escape valve that discharges the excess ventilation volume to atmosphere, reducing both the volume and the pressure to ventilate the patient.

Method to be able to determine the phase, frequency, efficiency, depth, thoracic compression ratios during CPR by detecting the flexion of a tube placed in the patient's mouth, the esophagus by various methods. Including, but not limited to, tube strain gauges, fiber optics, air movement sensors. • A method of timing ventilations at a certain stage of compression to maximize CPR efficiency while allowing adequate gas exchange. Using the technology mentioned in the previous method attached to the fan. • A method of continuing ventilations after compressions are stopped or paused. • A method of providing the handler with real-time information on the efficiency of rescuers' compressions through auditory or visual feedback.

Some of the features of the systems described above include: a method of placing electrodes on the tube and stimulating the heart through the tube placed in the mouth, esophagus, or trachea; a method of defibrillating the heart through electrodes placed in a tube in the mouth, trachea, or esophagus of a patient; and a method of determining whether the patient has a pulse through a tube in the patient's mouth, trachea, or esophagus.

Figures 19-28 illustrate an example of circuitry for detecting the phase, rate, depth, and effectiveness of a chest compression with a resistance located over an airway tube located in the mouth, trachea, or esophagus of the patient. patient. The information can be passed on to the rescuer or used to indicate a valve to time a ventilation. This is just one example of how to implement the invention described above without limiting other methods mentioned above in any way.

The foregoing simply illustrates the principles of the invention. It will be appreciated that those skilled in the art will be able to devise various arrangements which, although not explicitly described or shown herein, contain the principles of the invention and are included within its scope. Additionally, all examples and conditional language set forth herein are primarily intended to assist the reader in understanding the principles of the invention and the concepts contributed by the inventors to further the art, and such examples and conditions should be construed without limitation. specifically indicated. The scope of the present invention, therefore, is not intended to be limited to the exemplary embodiments shown and described herein. Rather, the appended claims contain the scope of the present invention.

It should be noted that, as used herein and in the appended claims, the singular forms a, an, and the include references to plurals unless the context clearly indicates otherwise. Thus, for example, reference to a chain may include a plurality of such chains and reference to the tubular member includes reference to one or more tubular members and equivalents thereof known to those skilled in the art, etc.

When a range of values ​​is provided, it is understood that each intermediate value is also specifically disclosed, up to one-tenth of the unit of the lower limit, unless the context clearly indicates otherwise, between the upper and lower limits of that range. The invention encompasses every smallest range between any set value or intermediate value in a set range and any other set or intermediate value in said set range. The upper and lower limits of these smaller ranges may be independently included or excluded in the range, and the invention also encompasses every range where either, neither, or both limits are included in the smaller ranges, subject to any limits specifically excluded in the set range. When the stated range includes one or both limits, the ranges that exclude one or both of said included limits are also included in the invention.

All publications mentioned herein disclose and describe the methods and / or materials in connection with which the publications are cited. The publications described herein are provided solely for disclosure prior to the filing date of this application. Nothing herein shall be construed as an acknowledgment that the present invention is not entitled to precede such publication due to prior invention. In addition, the publication dates provided may be different from the actual publication dates which may need to be confirmed independently.