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    • 专利摘要:
    The present invention relates to a respiratory assistance apparatus for providing a respiratory gas, such as air, to a patient during cardiopulmonary resuscitation (CPR) comprising a source (1) of breathing gas, a means for measuring CO2 (4), and signal processing and control means (5). The signal processing and control means (5) are configured to process the CO2 content measurement signals corresponding to measurements made by the CO2 content measuring means (4) for a given period of time (dt) and extracting a plurality of CO2 content values, selecting the maximum value (Vmax) of CO2 content from said plurality of CO2 content values, repeating these steps to obtain a plurality of successive maximum CO2 content values (Vmax) measured over a time window (Ft) comprising several successive time periods (dt), calculating at least one average value (Vmoy) of CO2 content from the maximum values (Vmax) of CO2 content obtained over the time window (Ft), and transmit said at least one average value (Vmoy) of CO2 content to the graphical user interface (7) which displays it.
    公开号:FR3076463A1
    申请号:FR1850225
    申请日:2018-01-11
    公开日:2019-07-12
    发明作者:Marceau RIGOLLOT；Jean-Christophe Richard；Bilal Badat
    申请人:Air Liquide Medical Systems SA；
    IPC主号:
    专利说明:

    Provided is a respiratory support device, i.e., a medical ventilator, connected to a patient receiving cardiopulmonary resuscitation (CPR), i.e., a patient undergoing cardiac arrest. a cardiac massage with alternating compressions of chest decompressions, with display of at least one average value of CO2 content obtained, over a given time window, from a plurality of successive maximum values of CO2 content.
    Mechanical ventilation medical devices, also called respiratory assistance devices or medical ventilators, are commonly used to supply respiratory gas, for example air enriched or not with oxygen, to certain patients suffering from respiratory disorders.
    The supply of respiratory gas to the patient is commonly operated by means of a motorized and controlled micro-blower, as in particular described by EP-A-3093498, EP-A-2947328, EP-A-2986856, EP-A-2954213 or EP-A-2102504.
    It is known to monitor the gaseous compounds present in the gas administered to patients, in particular in the gases exhaled by patients which contain CO2 resulting from pulmonary gas exchanges, that is to say CO2 produced by the patient's metabolism. , transported to the lungs through the bloodstream and then evacuated when the patient expires. Thus, the etCCh for End Tidal CO2 or CO2 at the end of expiration, corresponds to the measurement of the fraction of CO2 at the end of expiration in the gases collected during the expiration of an individual, whether his inspiration is natural or assisted, that is to say obtained by mechanical ventilation.
    Under mechanical ventilation, different techniques allow spectrophotometric analysis of the CO2 fraction of exhaled gases. To do this, the gas present in the expiratory circuit can be: - either aspirated and then analyzed by an analysis cell at a site remote from the respiratory circuit. This way of operating is called derivative or secondary flow, i.e. "sidestream" in English, - or analyzed near the patient, preferably at the level of a part Y arranged in the respiratory circuit near the patient. This way of operating is called main stream, i.e. "mainstream" in English.
    During cardiopulmonary resuscitation or CPR performed on a person with cardiopulmonary arrest, alveolar CO2 depends on the amount of CO2 generated by cell metabolism, cardiac output, and pulmonary ventilation / perfusion ratios. In theory, the more efficient the CPR, the more the cellular metabolism is preserved and the cardiac output generated by the chest compressions is important, the more the quantity of CO2 brought back to the lungs. For these reasons, monitoring of EtCO2 is recommended to guide CPR cardiopulmonary resuscitation.
    Figure 1 is a capnogram which is a graphical representation of the changes in CO2 content in a patient's breathing gas over time (in seconds). This type of capnogram is observed on patients ventilated outside of cardiac arrest situations. As we can see, it is divided into four successive phases: - Phase I: it represents the inspiratory baseline which must be stable at zero. - Phase II: it is the ascending part of the capnogram and corresponds to the appearance of CO2 in the exhaled gases, at the beginning of the patient's exhalation, by emptying the best ventilated alveoli. In reality, the expiration begins a little before this phase because the gas exhaled at the beginning of expiration is devoid of CO2 since it did not participate in gas exchanges, due to the instrumental and anatomical dead spaces. The increase in CO2 is slower the more the lungs are inhomogeneous and the alveoli have long time constants. - Phase III: it corresponds to the alveolar plateau phase which corresponds to the gas rich in CO2 coming from the least well ventilated alveoli. The maximum end of plateau value (PetCO2) corresponds to the value of etCC> 2. - Phase IV: it corresponds to the decrease in the CO2 concentration caused by the start of spontaneous or assisted inspiration (i.e. mechanical).
    However, during Cardiopulmonary Resuscitation (CPR) on a patient in cardiorespiratory arrest, the capnogram is very different for several reasons, in particular: - chest compressions (CTs) generate displacements of small volumes of gas. These volumes, close to the instrumental and anatomical dead space, disturb the capnogram between two ventilatory cycles by a CO2 washing effect. Oscillating patterns are thus often observed since the maximum value of CO2 on each chest compression does not cease to vary. - the dynamic opening and closing behavior of the small airways during CPR was recently reported during CPR. This phenomenon compromises the movement of exhaled gases and therefore the interpretation of CO2 concentrations during CPR.
    It is therefore understood that the etCO2 as it is currently measured, that is to say during each chest compression does not make it possible to obtain a reliable approximation of the alveolar CO2 content.
    However, this alveolar CO2 content is important for nursing staff because it is a reflection of the quality of CPR and of a possible resumption of spontaneous cardiac activity (RACS).
    Indeed, during CPR, the CO2 concentration value or the CO2 trend is used by the rescuer practicing cardiac massage, ie doctor or any other nursing staff, as an "image" of the blood circulation and therefore of the effectiveness of the cardiac massage that he practices, the CO2 trend being defined as a graphical representation of several CO2 concentration values measured successively over a given time window, for example during the 30 seconds to 5 minutes that have just elapsed.
    The recurring problem which results therefrom is that one or more measurements of the CO2 content without taking into account all or some of these factors, in particular the impact of the ventilation carried out on the patient in cardiac arrest, makes the use for prognosis of this unreliable or even completely unreliable CO2 measurement.
    Current etCO2 monitoring solutions are adapted to variations in CO2 caused by breathing, whether mechanical or spontaneous. The frequencies involved are of the order of 10 to 30 c / min. The algorithms and mechanisms used are adapted to these frequencies and to small variations in CO2 between two patient breaths.
    However, during cardiopulmonary resuscitation, the frequencies of the chest compressions (CTs) involved are of the order of 100 c / min, the volumes of gas mobilized low and the gas flows large and irregular.
    Under these conditions, the value of etCO2 varying with each chest compression which is displayed on the graphical interface of current ventilators, is refreshed at an inadequate frequency since the ventilators try to follow the evolution of CO2 at the massage frequency, or 100 c / min.
    In other words, the value of etCCh or the CO2 trend displayed by current ventilators is not representative of a CO2 concentration linked to the patient's metabolism because the origin of the gas analyzed is not guaranteed .
    Documents WO-A-2014/072981, US-A-2016/133160 and US-A-2012/016279 propose methods for monitoring the CO2 content in the gases exhaled by a patient undergoing CPR, in which the ventilators indicate to the rescuer that he must stop the cardiac massage when the etCÜ2 content is greater than 30 mm Hg for example.
    The problem that arises is therefore to provide a respiratory assistance device, that is to say an improved medical ventilator, which makes it possible to display, during CPR, a reliable CO2 value, that is to say - say which reflects as much as possible the alveolar CO2 and its changes over time, with the aim of better assisting the rescuer during CPR by offering him relevant information facilitating CPR monitoring and allowing or facilitating detection of RACS for example .
    The solution of the invention therefore relates to a respiratory assistance device, that is to say a medical ventilator, for supplying respiratory gas, such as air, to a patient during cardiopulmonary resuscitation (CPR). comprising: - a source of respiratory gas for supplying respiratory gas to said patient during cardiopulmonary resuscitation (CPR), - means for measuring CO2 content for carrying out measurements of concentration of CO2 produced by said patient, and providing CO2 content measurement signals to signal processing and control means, signal processing and control means configured to process the CO2 content measurement signals coming from the CO2 content measurement means, and - at least one graphical user interface or IGU, characterized in that: - the signal processing and control means are configured to: a) process the CO2 content measurement signals corresponding to op measurements erected by the CO2 content measurement means for a given period of time (dt), in order to extract a plurality of CO2 content values therefrom, b) selecting the maximum value (Vmax) of CO2 content from said plurality of values of CO2 content measured during said given time period (dt), c) repeat steps a) and b) to obtain several maximum values (Vmax) of successive CO2 content measured during a time window (Ft) comprising several periods of successive times (dt), d) calculating at least one average value (Vmoy) of CO2 content from the maximum values (Vmax) of CO2 content obtained over the time window (Ft), and e) transmitting said data to the at least one average value (Vmoy) of CO2 content at the graphical user interface or IGU, - and the graphical user interface is configured to display said at least one average value (Vmoy) for CO2 content.
    Depending on the case, the respiratory assistance device of the invention may include one or more of the following technical characteristics: - the IGU is configured to display at least one value of CO2 content supplied by the processing means signal and steering. - the IGU is configured to display said at least one average value (Vmoy) of CO2 content in the form of a numerical value or a graphic representation, preferably a graphic representation, for example curve, bar graph or other . - the IGU is configured to display the most recent average value (Vmoy) of CO2 content, i.e. the last value calculated over a given time window (Ft), in particular a time window ( Ft) slippery. - the IGU is further configured to display the most recent maximum value (Vmax) of CO2 content, i.e. the last maximum value (Vmax) of CO2 content determined during the last period of time ( dt) of a given time window (Ft) including several successive time periods (dt), in particular a sliding time window (Ft). - the CO2 produced by the patient. This CO2 is observed during the expiration of the patient, that is to say in particular in the exhaled gases, or rebreathed on the next inspiration when it is a question of gas trapped in a part of the respiratory circuit, for example between a junction piece arranged upstream of the respiratory interface, such as a Y piece, and the CO2 sensor. - according to one embodiment, the IGU is configured to display at least a portion of the successive average values (Vmoy) of CO2 content calculated in the form of a curve formed by a succession of graphic symbols, each graphic symbol corresponding to an average value (Vmoy) of CO2 content, in particular a trend curve. - each average value (Vmoy) of CO2 content is displayed by the IGU in the form of a graphic symbol of point, cross or any other symbol. - according to another embodiment, the IGU is configured to display at least a portion of the successive average values (Vmoy) of CO2 content calculated in the form of a bar graph comprising several bars, each bar of said corresponding bar graph at an average value (Vmoy) of CO2 content. preferably, the graphic display, in particular of the trend curve or the like, representing the variations in the average CO2 content (Vmoy) is refreshed, that is to say updated, after a regular time interval and cyclic, for example after a few seconds. - the signal processing and control means are configured to repeat steps a) to e) so as to obtain several average values (Vmoy) of successive CO2 content calculated from maximum values (Vmax) of CO2 content obtained on successive time windows (Ft), in particular a sliding time window. - The successive time windows (Ft) are advantageously a sliding time window. - The time window (Ft) is between 20 seconds and 10 minutes, preferably between 30 seconds and 5 minutes, preferably at least 1 minute. - the IGU is configured to display a trend curve formed by a succession of graphic symbols, each succession of graphic symbols corresponding to an average value (Vmoy) of CO2 content. In other words, the IGU displays on a time graph representing a graphic representation of each average value (Vmoy) of CO2 content, namely a graphic symbol of point or cross type for example, as a function of time (in seconds or minutes). This display is done on a sliding time window ranging from 30 sec to 5 minutes for example, in particular from 1 to 3 minutes. - The source of respiratory gas is a source of air, in particular a motorized micro-blower, also called turbine or compressor. - The signal processing and control means comprise at least one electronic card. - The signal processing and control means comprise at least one microprocessor, preferably a microcontroller. - the microprocessor implements at least one algorithm. - the CO2 content measurement means are preferably arranged on the main gas flow, ie in "mainstream". - alternatively, the means for measuring the CO2 content are arranged in the fan, i.e. in “sidestream”, the gas sample or samples being taken from the main flow, then analyzed to determine the CO2 content. - the source of respiratory gas is in fluid communication with a gas conduit serving to convey the respiratory gas towards the patient, i.e. up to a respiratory interface. - The gas pipe is in fluid communication with a respiratory interface so as to supply said interface with gas coming from the micro-blower. the means for measuring the CO2 content are electrically connected to the signal processing and control means. - The CO2 content measurement means are arranged so as to carry out CO2 concentration measurements downstream of the gas pipe, preferably at a downstream end of the gas pipe. the means for measuring the CO 2 content are arranged upstream and in the immediate vicinity of the respiratory interface, that is to say close to the mouth of the patient. - The CO2 content measurement means are arranged on a junction piece arranged between the respiratory interface and the gas conduit. - The CO2 content measurement means are arranged on a junction piece arranged between the respiratory interface and a Y-piece comprising internal gas passages. - the respiratory interface is an endotracheal intubation probe, a facial mask or a laryngeal mask, also called a supra-glottic device, or any suitable device for administering gas. - The respiratory interface is preferably an endotracheal intubation probe, commonly called a 'tracheal probe'. - According to a first embodiment, the means for measuring the CO2 content are arranged on a junction piece arranged upstream of the respiratory interface, preferably between the respiratory interface and the downstream end of the gas conduit, particular between the respiratory interface and a Y-piece with internal gas passages. - Preferably, the means for measuring the CO2 content are arranged on a junction piece comprising an internal gas passage. - According to a second embodiment, the means for measuring the CO2 content are arranged in the device, that is to say in the carcass of the device, by being connected, via a gas sampling pipe or similar to a gas sampling site located upstream and in the immediate vicinity of the respiratory interface. in particular, the means for measuring the CO2 content are fluidly connected to a gas sampling site carried by a junction piece, in particular arranged between the respiratory interface and the gas conduit, typically between the respiratory interface and a downstream end of said gas pipe. - The junction piece is fluidly connected between the intermediate connecting piece, that is to say a Y-piece, and the respiratory interface. - It includes a patient circuit comprising an inspiratory branch allowing gas to be conveyed to the patient and an expiratory branch making it possible to evacuate the gas exhaled by the patient. - the inspiratory branch, the expiratory branch and the respiratory interface are connected mechanically and / or fluidically, directly or indirectly, to an intermediate connecting piece, in particular a Y-piece. - the gas duct forms all or part of the branch inspiratory of the gas circuit. - the expiratory branch communicates fluidically with the atmosphere to evacuate the gas exhaled by the patient, in particular a gas rich in CO2. - the inspiratory branch and / or the expiratory branch include flexible tubes. - Preferably, all or part of the gas pipe forming all or part of the inspiratory branch of the gas circuit is a flexible pipe. the means for measuring the CO 2 content are arranged so as to carry out measurements of the CO 2 concentration in or at the outlet of the inspiratory branch of the gas circuit. - The signal processing and control means are configured to control the source of respiratory gas and deliver the respiratory gas according to successive ventilatory cycles, in particular ventilatory cycles comprising two pressure levels. - the given period of time (dt) is several seconds. - each ventilatory cycle includes a BP phase (Dbp) during which the gas is delivered by the micro-blower at a pressure called low or low pressure (BP), and an HP phase (Dhp) during which the gas is delivered by the micro -blower at a pressure called high or high pressure (HP), with HP> BP. - The micro-blower is controlled to supply gas at a low pressure (BP) between 0 and 20 cm of water, preferably between 0 and 15 cm of water, more preferably 0 and 10 cm of water. - the micro-blower is controlled to supply gas at a high pressure (HP) between 5 and 60 cm of water, preferably between 5 and 45 cm of water, preferably still 5 and 30 cm of water (with HP> BP). - the BP phase has a duration greater than the HP phase. - the BP phase has a duration of between 2 and 10 seconds, typically of the order of 3 to 6 seconds. - The HP phase has a duration of between 0.5 and 3 seconds, typically of the order of 1 to 2 seconds. - the given period of time (dt) is several seconds. - the time period (dt) is between 2 and 10 seconds, typically of the order of 3 to 6 seconds. - the period of time (dt) corresponds to the duration of the BP phase of each ventilatory cycle. - the total duration of a ventilation cycle is between 3 and 12 seconds. - the given period of time (dt) encompasses several durations of chest compressions and successive relaxations, typically between 5 and 20 chest compressions. - the CO2 content measurement means are configured to operate continuous measurements. - The CO2 content measurement means include a CO2 sensor. - The CO2 content measurement means include a capnometer as a CO2 sensor. - The CO2 content measurement means comprise a CO2 sensor, the measurement of which is in fluid communication with the interior or lumen of the junction piece arranged upstream of the respiratory interface. - It includes storage means cooperating with the signal processing and control means for storing the plurality of CO2 content values measured during the given time period. - It includes storage means cooperating with the signal processing and control means to store maximum (Vmax) and / or average (Vmoy) values of CO2 content. - The storage means include a flash memory or hard drive type. - It further comprises gas flow measurement means configured to operate at least one measurement, preferably continuously, of the flow of expired gas and of the flow of gas inspired by the patient. The flow allows monitoring and surveillance of chest compressions, as well as calculation, monitoring and surveillance of the volumes of gas delivered and exhaled (ventilator and CTs). - The gas flow measurement means comprise a flow sensor. - the graphical user interface (IGU) includes a digital screen, preferably a touch screen. - the screen includes several tactile keys activating different functions and / or several zones or display windows. - the screen is of the type with color display. - It comprises a source of electric current, for example a battery or the like, preferably a rechargeable battery. - It includes alarm means configured to trigger when the maximum (Vmax) or average (Vmoy) value of CO2 content exceeds a threshold value. the alarm means include an audible or visual alarm, or both. - the alarm means are programmed to be triggered when the maximum value (Vmax) of CO2 measured, at an instant t, is such that: [VmaxCCk]> n x [MoyCCk], where:. n is between 1.20 and 2, preferably between 1.25 and 1.7, for example of the order of 1.5,. [VmaxCCk] is the maximum value of CO2 content measured during a given time dt, for example over a time dt between 2 and 10 seconds,. [MoyCCk] is the average value of the maximum values of CO2 content [VmaxCCk] determined for several successive durations dt included in a given time window (FT) (FT> x.dt with x> 2), for example a period of 30 sec to 5 minutes, or more. - It comprises a rigid carcass comprising the source of respiratory gas, the signal processing and control means, the source of electric current and the storage means. - The IGU is arranged, in particular embedded, in one of the walls forming the carcass of the fan. - The rigid carcass is formed in whole or in part from polymer. - The CO2 content measurement means are configured to operate successive CO2 concentration measurements over successive periods of time (dt), that is to say periods of time (dt) spaced from each other. - The CO2 content measurement means are configured to operate successive CO2 concentration measurements over successive periods of time (dt) during successive ventilation cycles, in particular during the BP phases of successive ventilation cycles. The invention also relates to a method (ie, a method) for monitoring cardiopulmonary resuscitation (CPR) operated on a patient in cardiac arrest, in which: - a respiratory assistance device comprising a source is used respiratory gas, such as a micro-blower, to supply respiratory gas to a patient during cardiopulmonary resuscitation (CPR), - measurements of the CO2 concentration produced by said patient are carried out, for example by means of a capnometer , - the CO2 content measurement signals are processed, for example by means of signal processing and control means, such as a microprocessor, - a plurality of CO2 content values measured over a period of time (dt) is determined ) given, - the maximum value (Vmax) of CO2 content is selected from the plurality of values of CO2 content, - the previous steps are repeated to obtain several maximum values (Vmax) of successive CO2 content m measured over a time window (Ft) comprising several successive time periods (dt), - at least one average value (Vmoy) of CO2 content is calculated from the maximum values (Vmax) of CO2 content obtained on the window time (Ft), and - said at least one average value (Vmoy) of CO2 content is displayed on an IGU. The invention will now be better understood thanks to the following detailed description, given by way of illustration but not limitation, with reference to the appended figures in which: - Figure 1 is a graphic representation of the variations in CO2 content in the respiratory gases d 'a normal patient, - Figure 2 shows a ventilatory cycle with two pressure levels that can be implemented by the device of Figure 6 to ventilate a patient in cardiopulmonary arrest during CPR, - Figure 3 illustrates the pressure variations at the pulmonary level in a patient in cardiopulmonary arrest during a CPR, - Figure 4 shows diagrammatically the quantity of CO2 measured by the capnometer of the device of Figure 6 during a CPR, and at the time and after return to spontaneous cardiac activity (RACS), - Figure 5 shows diagrammatically the peaks of CO2 content during the ventilatory cycles implemented during CPR, - Figure 6 is a diagram of an embodiment of a respiratory assistance device for CPR according to the invention, and - Figure 7 shows schematically the measurements and time intervals used for the calculation and display of the CO2 trend.
    FIG. 6 is a schematic representation of an embodiment of a respiratory assistance device or medical ventilator according to the invention used to supply a respiratory gas, typically air or air enriched with oxygen, to a patient P during cardiopulmonary resuscitation (CPR), that is to say a person in cardiac arrest on whom a rescuer performs a cardiac massage, with alternating chest compressions (CT) and relaxations (Re), that is to say non-chest compressions. The apparatus comprises a source 1 of respiratory gas, such as a motorized micro-blower, which is in fluid communication with a gas conduit 2 of the inspiratory branch 2a of the patient circuit 2a, 2b to supply the respiratory gas to said patient P during the RCP.
    The source 1 of respiratory gas is controlled, that is to say controlled, by signal processing and control means 5, in particular an electronic microprocessor card 6 or the like. The signal processing and control means 5 control the source 1 of respiratory gas so that it delivers the gas according to one (or more) predefined ventilation mode.
    Preferably, it makes it possible to control the gas source 1 to deliver the gas according to a "normal" ventilatory mode corresponding to a ventilation of a patient who is not in cardiac arrest and a "CPR" ventilatory mode corresponding to a ventilated '' a patient who is in cardiac arrest and on whom a rescuer starts or performs CPR.
    For example, according to a ventilation mode dedicated to CPR, the source 1 of respiratory gas is controlled to supply the respiratory gas, typically air, according to a ventilation cycle comprising several pressure levels or of “BiPAP” type, such as illustrated in Figure 2, in particular 2 pressure levels comprising a low pressure level, for example a low pressure (BP) of between approximately 0 cm H2O and 15 cm H2O, and a high pressure level, for example a high pressure ( HP) between approximately 7 cm H2O and 40 cm H2O.
    The gas is delivered alternately between these two pressure levels (BP, HP), as illustrated in Figure 2, throughout the CPR by the rescuer, that is to say while the rescuer operates the CTs and relaxations. The duration (Dbp) of supply of gas at low pressure (BP) by the micro-blower 1 is between 2 and 10 seconds, typically of the order of 3 to 6 seconds, while the duration (Dhp) of supply of the high pressure gas (HP) is less than 3 seconds, for example of the order of 0.5 to 1.5 seconds.
    The chest compressions (CTs) and loosening (Re) resulting from the cardiac massage will themselves cause pressure variations in the patient's lungs which will increase or decrease the pressure supplied by the microsuffler 1 and this results in patient's lungs, a pressure curve as illustrated in Figure 3 where the pressure peaks at the high (ie at PH) and low (ie at PB) plateaus reflect the chest compressions (CT) with increased pressure since the thorax s subsides under the pressure of the CT operated by the rescuer, and releases (Re) with low pressure since the thorax rises in the absence of CT.
    As seen in Figures 2 and 3, the given period of time (dt), during which the plurality of CO2 content values is measured and the maximum CÜ2 content value (Vmax) is extracted corresponds to the duration ( Dbp) for supplying gas at low pressure (BP), ie between 2 and 10 seconds, typically between 3 and 6 seconds.
    The gas supplied by the micro-blower 1 is conveyed by the gas conduit 2 which forms all or part of the inspiratory branch 2a of the patient circuit 2a, 2b. The respiratory gas, in general air, is supplied to the patient via a gas distribution interface, for example here an endotracheal intubation probe 3, more simply called 'tracheal probe'. However, other interfaces can be used, in particular a facial mask or a laryngeal mask.
    The gas pipe 2 of the inspiratory branch 2a is in fluid communication with the tracheal tube 3 so as to supply it with gas, such as air, coming from the source of respiratory gas 1. The gas pipe 2 actually comes connect to the tracheal tube 3 via an intermediate connection part, typically a part 8 in Y comprising internal passages for the gas. This intermediate connection piece 8 in Y includes internal gas passages.
    The part 8 in Y is also connected to the expiratory branch 2b of the patient circuit 2a, 2b so as to be able to collect and convey the gases rich in CO2 exhaled by the patient P and evacuate them to the atmosphere (at 9).
    There are also provided means for measuring the CO2 content 4, called the CO2 sensor or more simply a capnometer, designed to carry out measurements of the concentration of CO2 in the gas exhaled by the patient P, and supply the signals for measuring the content of the CO2. CO2 corresponding to the signal processing and control means 5 where these measurement signals can be processed by a (or) calculation algorithm or the like.
    In the embodiment of FIG. 6, the CO2 sensor is arranged near the mouth of patient P in the “main stream” configuration, that is to say upstream and in the immediate vicinity of the interface respiratory 3, preferably between the intermediate connection piece 8, ie the Y-piece, and the respiratory interface 3, ie the tracheal tube, for example on a junction piece 18 (cf. FIG. 6).
    According to another embodiment (not shown), the CO2 sensor can be arranged in a “derivative flow” configuration (sidestream). In this case, the CO2 sensor 4 is located in the carcass of the respiratory assistance device and is connected, via a gas sampling line, such as a tube or the like, to a gas sampling site located upstream. and in the immediate vicinity of the respiratory interface 3, for example on the junction piece 18. This gas sampling line communicates fluidly with the lumen of the junction piece 18 so as to be able to take gas there and then convey it to the CO2 sensor located in the casing of the device.
    In all cases, the junction piece 18 includes an internal gas passage allowing the gas to pass through it.
    Preferably, the CO2 sensor operates continuous measurements of the CO2 concentration in the gas circulating through the junction piece 18, which gas is enriched in CO2 during its passage through the lungs of patient P where gas exchanges.
    The CO2 content measurement signals are then transmitted by the CO2 sensor, by electrical connection or the like, in particular wired or other, to the signal processing and control means 5.
    Indeed, monitoring of the CO2 content, in particular of etCO2 which indirectly reflects the alveolar CO2 content, is of great importance during CPR, in particular to detect an RACS. Indeed, a return of spontaneous cardiac activity (RACS), therefore a significant increase in cardiac output, generates a rapid increase in the amount of CO2 brought by the blood to the lungs and transferred through the alveolo-capillary membrane, this CO2 then ending up in the gas flow exhaled by the patient.
    From there, according to the present invention and as illustrated in FIG. 7, the signal processing and control means 5 are configured, in particular the microprocessor 6, for: a) processing the CO2 content measurement signals corresponding to measurements operated by the CO2 content measurement means 4, typically a capnometer, for a given period of time (dt), for example between 1 and 7 seconds, and extracting a plurality of CO2 content values therefrom. During the period of time (dt) considered, the patient is subjected to a cardiac massage with a succession of CTs and relaxations, which generates gas inflows and outflows from the lungs, therefore variations in CO2 contents in the exhaled gas flow. , that is to say leaving the lungs under the effect of the CTs, in particular as a function of the force applied by the rescuer which is not equal from one contraction to the other, as illustrated in FIGS. 3 and 5 for example. b) selecting the maximum value (Vmax) of CO2 content from said plurality of CO2 content values measured during said given time period (dt). In other words, among the different CO2 contents measured during the time period dt, only the highest is selected which is the most representative of the CO2 content, ie in EtCCL, during the time period (dt) considered. . To do this, the signal processing and control means 5 memorize and then compare the measured CO2 values with each other so as to retain only the highest. c) repeat steps a) and b) to obtain several maximum values (Vmax) of successive CO2 content measured during a longer time window (Ft), for example between 30 seconds and 5 minutes, comprising several time periods ( dt) successive. In other words, the signal processing and control means 5 operate measurements for several successive periods (dt) and for each of them, select the maximum CO2 content value over each of the desired periods obtained during the window long time including said successive periods (dt). All these maximum CO2 content values are memorized by the storage means 11. d) calculating at least one average value (Vmoy) of CO2 content from the maximum values (Vmax) of CO2 content obtained over the time window (Ft). The maximum values (Vmax) of CO2 content which have been stored over the entire long time window (Ft) are found in the storage means 11, then an average value of CO2 content is calculated from these for the time window (Ft) considered. e) transmitting said at least one average value (Vmoy) of CO2 content to the IGU 7, which then displays this average value (Vmoy) of CO2 content in the form of a numerical value or a graphic representation, advantageously in the form of a graphical representation, namely a graphical symbol, for example a point, a cross or any other symbol, which is displayed on a time graph representing the graphical representation of the average value (Vmoy) of CO2 content function of time. f) steps a) to e) are repeated as many times as necessary over successive periods of time (dt) and over a sliding time window (FT) of duration typically between 1 and 5 minutes, so as to obtain average values (Vmoy) of CO2 content over time making it possible to follow the evolution of the CO2 content in the gas flow leaving the patient's lungs during cardiac massage, in particular under the effect of CTs. In other words, the IGU 7 displays for example a trend curve formed by a succession of graphic symbols. Of course, another graphical representation could be adopted, such as bar graphs or the like.
    The medical ventilator of the invention allows a measurement, advantageously continuously, of the CO2 concentration in the gases exhaled by the patient P. The measurement is carried out by the capnometer 4 which is arranged on the path of the gas, as close as possible to the mouth of the patient P, preferably between the Y-shaped part 8 and the respiratory interface 3, and the measurement signals are transmitted, via electrical or other connections, to the signal processing and control means 5.
    This measurement of the CO2 concentration in the gases exhaled by the patient P makes it possible to obtain a plurality of maximum values (Vmax) of CO2 content which are then processed by the signal processing and control means 5 to calculate values CO2 content averages (Vmoy) from several successive maximum CO2 content values (Vmax) obtained over a given time window comprising several successive given time periods during which the maximum CO2 content values (Vmax) were determined, preferably a sliding time window (see Fig. 7).
    The average value (Vmoy) of CO2 is not necessarily updated when each point is displayed, but can be refreshed and displayed after a defined time, for example a few seconds.
    Indeed, as already explained, the CO2 concentration value which most reflects the alveolar CO2 content, and which therefore gives a good indication of the state of the blood circulation in patient P during CPR, is the value the highest CO2, also called maximum peak value, as illustrated in Figure 5 which shows the evolution of the CO2 content and of the etCO2 measurements, for given durations (dt), within the framework of a CPR performed on a person in cardiac arrest.
    More specifically, during CPR, the CO2 content in the gas exhaled by the patient due to the cardiac massage performed, varies depending on the presence or not of chest compressions (CTs).
    Thus, during the blowing of air by the micro-blower 1 of the fan, then during the first compression (s) following this blowing, no CO2 is detected in the gas flow conveyed by the duct 2 to the room. 8 in Y, then in the tracheal tube 3 which then distributes this air to the lungs of patient P. After some chest compressions (CT) performed by a rescuer, CO2 is detected at room 8 in Y by the capnometer 4 since alternating CT and relaxation (Re) generate movements of air entering and leaving the patient's lungs.
    Exhaled air rich in CO2 is then found in the room 8 in Y and measurements of CO2 concentrations can be carried out by the capnometer 4. The corresponding signals are sent to the signal processing and control means 5 where they are treated as explained above.
    The maximum value Vmax of CO2 determined during the durations (dt) given, for example durations of 3 to 7 seconds, is the one which best represents the alveolar CO2. Indeed, the CO2 present at the level of part 8 in Y is "washed" little by little because of the successive and repeated chest compressions, and tends to decrease after having reached this maximum value since the CT also generate evacuation towards the atmosphere (in 9) of gases rich in CO2, via the expiratory branch 2b of the patient circuit. Successive CTs therefore generate different levels of CO2, the most representative being the maximum peak value, as illustrated in Figure 5 which shows the evolution of the CO2 content in the gas and illustrates several measurements of etCCk measured over several durations dt successive, for example durations of 3 to 6 seconds, during the performance of a CPR. We can see that the CO2 content of the gas is not constant during a given time interval dt and that there is therefore necessarily a maximum value (Vmax) of CO2 content over each interval dt, i.e. say the peak value.
    The fan stores (in 11) therefore all the values of CO2 peaks during each time period dt, typically between 3 and 7 seconds, and determines the maximum value Vmax of CO2 content among the plurality of peaks (EtCO2_i, EtCO2_2, EtCO2_3 , ..., EtCO2_x) measured over a given period of time (dt), as illustrated in Figure 5.
    As illustrated in Figure 7, these operations are repeated over time over several successive given time periods (dt) included in a longer time window (Ft), for example a time window (Ft) from 30 sec to 5 min, advantageously a sliding time window (Ft), so as to be able to determine and display on the IGU 7, preferably continuously, a plurality of average values of CO2 content (Vmoy) in the form of a graphic representation, preferably a trend curve over time, on which graphic symbols represent the different average values of CO2 content (Vmoy) as a function of time, as illustrated in Figure 4.
    Furthermore, these maximum values Vmax of CO2 content are processed by the signal processing and control means 5 so as to calculate a succession of average values Vmoy of CO2 content, over a given time window, comprising several periods of successive given times during which said maximum values Vmax of CO 2 content have been determined, preferably a sliding time window, for example a time window between 30 seconds and 5 minutes.
    The average values Vmoy of CO2 content thus determined are displayed on the IGU 7 also in the form of a graphic representation, such as a curve, a bargraph or the like, preferably in the form of a trend curve on which the average values (Vmoy ) are represented by a succession of symbols, such as dots or the like (Fig. 4).
    In Figure 4, the curve "......" represents the values of Vmoy and the curve "_" represents the values of Et-C02.
    The data calculated from this CO2, in particular the values of Vmoy, constitute a useful indicator for the rescuer, allow him to control the CPR, since it reflects the state of the circulation and the metabolism of the patient from the moment when the patient is intubated (INT) and a CPR is performed (see Fig. 4). In fact, the more effective the RCP is, the greater the quantity of CO2 produced and transferred through the alveolo-capillary membrane and therefore the greater the quantity of CO2 that can be detected at the capnometer 4.
    From there, in case of return to spontaneous cardiac activity (RACS), the circulation resumes suddenly and therefore the quantity of alveolar CO2 increases in parallel, which induces a significant increase the quantity of CO2 perceived by the capnometer 4 by a factor often greater than 2, as illustrated in Figure 4. Indeed, we see in Figure 4 that the EtCCL is always less than 2.5 during CPR, but that it increases (AUG) suddenly until reaching more than 5 at RACS time, approximately 3 to 4 minutes after the patient's intubation (INT) and the start of CPR.
    In the context of the invention, the fact of displaying on the IGU 7 a trend curve based on the mean values Vmoy determined over a sliding time window (Ft) allows the rescuer to better detect the occurrence of the RACS since the Vmoy curve shows a strong increase (AUG in Fig. 4) at the time of a RACS due to the increased release of CO2 by the lungs being found in the exhaled gases.
    Thus, when the rescuer finds a sharp rise (AUG) in the curve of mean values Vmoy in CO2 on the IGU 7, the latter can conclude that the patient is at the start of RACS and can for example decide to analyze the rhythm cardiac and possibly to stop the cardiac massage.
    The fan also makes it possible to operate in parallel a continuous measurement of the flow rates of the exhaled and inspired gases, using a flow rate sensor (not shown).
    Advantageously, the ventilator of the invention can also include alarm means designed and programmed to warn the rescuer or the like when one (or more) maximum measured value of CO2 exceeds or, conversely, becomes lower than a given value. , prefixed or calculated continuously.
    In particular, an audible and / or visual alarm is provided which is triggered when the maximum measured value of CO2, at an instant t, is greater than a threshold value, for example: [VmaxCCk]> 1.5 x [MoyCCfi] where: [VmaxCCk] is the maximum value of CO2 content measured for a given period dt, for example over a period dt of between 2 and 10 seconds, [MoyCCk] is the average value of the maximum values of CO2 content [VmaxCCk] determined for several successive durations dt included in a given time window (FT) (FT> x.dt with x> 2), for example a period of 30 sec to 5 minutes, or more.
    Similarly, the alarm can be triggered in the event of a sudden drop in the CO2 concentration below a given minimum value which could be a sign of a new cardiac arrest of the patient, hyperventilation or an obstruction of the circuit gas between the patient and the machine, for example a flexible pipe bent or crushed and no longer allowing the gas to pass.
    A source of electric current 10, such as a rechargeable battery or the like, integrated into the casing of the fan, supplies, directly or indirectly, with electric current the signal processing and control means 5, the micro-blower 1, the IGU 7 or any other element of the device, in particular a memory 11. In general, the invention relates to a medical ventilator suitable for use during cardiopulmonary resuscitation (CPR) comprising a source of respiratory gas 1, such as a micro-blower, means for measuring the CO2 content 4, such as a capnometer, signal processing and control means 5 receiving and processing the signals for measuring the CO2 content coming from the means for measuring the CO2 content 4 to obtain maximum values (Vmax) of successive CO2 content measured over a time window (Ft), and calculate at least one average value (Vmoy) of CO2 content from the maximum values (Vmax) of CO2 content obtained on the time window (Ft), and an IGU 7 configured to display said at least one average value (Vmoy) of CO2 content. The respiratory assistance device or medical ventilator according to the present invention is particularly suitable for implementation during cardiopulmonary resuscitation (CPR) on a person (ie a patient) in cardiopulmonary arrest, in the context of which a breathing gas, such as pressurized air, is supplied according to a ventilatory cycle with several pressure levels to said person undergoing cardiac massage with alternating chest compressions and relaxations. To facilitate its transport by first aid workers, for example a doctor, a nurse, a firefighter or the like, the ventilator of the invention is preferably arranged in a transport bag.
    权利要求:
    Claims (14)
    [1" id="c-fr-0001]
    claims
    1. Respiratory assistance apparatus for supplying respiratory gas to a patient during cardiopulmonary resuscitation (CPR) comprising: - a source (1) of respiratory gas for supplying respiratory gas to said patient during cardiopulmonary resuscitation (CPR) ), - CO2 content measurement means (4) for carrying out measurements of the concentration of CO2 produced by the patient, and supplying CO2 content measurement signals to signal processing and control means (5) , - signal processing and control means (5) configured to process the CO2 content measurement signals coming from the CO2 content measurement means (4), and - at least one graphical user interface (7), characterized in that: - the signal processing and control means (5) are configured to: a) process the CO2 content measurement signals corresponding to measurements carried out by the CO2 content measurement means (4) during a period of t given emps (dt), and extracting a plurality of CO2 content values therefrom, b) selecting the maximum value (Vmax) of CO2 content from said plurality of CO2 content values measured during said given period of time (dt) , c) repeat steps a) and b) to obtain several maximum values (Vmax) of successive CO2 content measured over a time window (Ft) comprising several successive time periods (dt), d) calculate at least one value average (Vmoy) of CO2 content from the maximum values (Vmax) of CO2 content obtained over the time window (Ft), and e) transmitting said at least one average value (Vmoy) of CO2 content to the graphical user interface (7), and the graphical user interface (7) is configured to display said at least one average value (Vmoy) of CO2 content.
    [2" id="c-fr-0002]
    2. Apparatus according to the preceding claim, characterized in that the signal processing and control means (5) are configured to repeat steps a) to e) so as to obtain several average values (Vmoy) of successive CO2 content calculated from maximum values (Vmax) of CO2 content obtained over successive time windows (Ft), preferably a sliding time window (Ft).
    [3" id="c-fr-0003]
    3. Apparatus according to one of the preceding claims, characterized in that the time window (Ft) is between 20 seconds and 10 minutes, preferably between 30 seconds and 5 minutes.
    [4" id="c-fr-0004]
    4. Apparatus according to one of the preceding claims, characterized in that the graphical user interface (7) is configured to display said at least one average value (Vmoy) of CO2 content in the form of a graphical representation or a numerical value, preferably in the form of a graphical representation.
    [5" id="c-fr-0005]
    5. Apparatus according to one of the preceding claims, characterized in that the graphical user interface (7) is configured to display at least a portion of the successive average values (Vmoy) of CO2 content calculated in the form of: - a curve formed by a succession of graphic symbols, each graphic symbol corresponding to an average value (Vmoy) of CO2 content, - or of a bar graph comprising several bars, each bar of said bar graph corresponding to an average value ( Vmoy) of CO2 content.
    [6" id="c-fr-0006]
    6. Apparatus according to one of the preceding claims, characterized in that the signal processing and control means (5) comprise at least one microprocessor.
    [7" id="c-fr-0007]
    7. Apparatus according to one of the preceding claims, characterized in that the means for measuring the CO2 content (4) comprises a capnometer.
    [8" id="c-fr-0008]
    8. Apparatus according to one of the preceding claims, characterized in that the source (1) of respiratory gas is in fluid communication with a gas conduit (2), the gas conduit (2) being in fluid communication with an interface respiratory (3), preferably an endotracheal intubation tube, a face mask or a laryngeal mask.
    [9" id="c-fr-0009]
    9. Apparatus according to one of the preceding claims, characterized in that the means for measuring the CO2 content (4) are arranged: - either upstream and in the immediate vicinity (18) of the respiratory interface (3), - either in the device by being connected to a gas sampling site (18) located upstream and in the immediate vicinity of the respiratory interface (3).
    [10" id="c-fr-0010]
    10. Apparatus according to one of the preceding claims, characterized in that the given time period (dt) is between 2 and 10 seconds, typically of the order of 3 to 6 seconds.
    [11" id="c-fr-0011]
    11. Apparatus according to one of the preceding claims, characterized in that the means for measuring the CO2 content (4) are configured to operate measurements continuously.
    [12" id="c-fr-0012]
    12. Apparatus according to one of the preceding claims, characterized in that it comprises storage means (8) cooperating with the signal processing and control means (5) for storing the CO2 content values measured during each given time period (dt) and maximum values (Vmax) of CO2 content calculated for each time window (Ft).
    [13" id="c-fr-0013]
    13. Apparatus according to one of the preceding claims, characterized in that the graphical user interface (IGU) comprises a digital screen, preferably a touch screen.
    [14" id="c-fr-0014]
    14. Apparatus according to one of the preceding claims, characterized in that the signal processing and control means (5) are configured to control the source (1) of respiratory gas and deliver the respiratory gas according to ventilatory cycles comprising two pressure levels, preferably the source (1) of breathing gas includes a motorized micro-blower.
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    同族专利:
    公开号 | 公开日
    ES2859563T3|2021-10-04|
    EP3510924A1|2019-07-17|
    CA3024430A1|2019-07-11|
    JP2019122758A|2019-07-25|
    US20190209796A1|2019-07-11|
    BR102018074807A2|2019-07-30|
    CN110025864A|2019-07-19|
    FR3076463B1|2019-11-29|
    EP3510924B1|2020-12-30|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    WO2012114286A1|2011-02-22|2012-08-30|Koninklijke Philips Electronics N.V.|Capnography system for automatic diagnosis of patient condition|
    WO2012162048A1|2011-05-23|2012-11-29|Zoll Medical Corporation|Medical ventilation system with ventilation quality feedback unit|
    US20150328417A1|2012-12-18|2015-11-19|Dräger Medical GmbH|Ventilation system|
    DE202020106081U1|2020-08-06|2020-11-05|Isis Ic Gmbh|Health hazard traffic light - CO2 measurement and display to show a potential hazard in rooms and buildings and for documentation in a cloud system|
    DE102020004765A1|2020-08-06|2022-02-10|Isis Ic Gmbh|Health hazard traffic light - CO² measurement and display to show a hazard potential in rooms and buildings and for documentation in a cloud system|
    法律状态:
    2019-01-24| PLFP| Fee payment|Year of fee payment: 2 |
    2019-07-12| PLSC| Search report ready|Effective date: 20190712 |
    2020-01-21| PLFP| Fee payment|Year of fee payment: 3 |
    2021-01-21| PLFP| Fee payment|Year of fee payment: 4 |
    优先权:
    申请号 | 申请日 | 专利标题
    FR1850225|2018-01-11|
    FR1850225A|FR3076463B1|2018-01-11|2018-01-11|VENTILATION APPARATUS FOR CARDIO-PULMONARY REANIMATION WITH CO2 TREND DISPLAY|FR1850225A| FR3076463B1|2018-01-11|2018-01-11|VENTILATION APPARATUS FOR CARDIO-PULMONARY REANIMATION WITH CO2 TREND DISPLAY|
    EP18206041.8A| EP3510924B1|2018-01-11|2018-11-13|Ventilation apparatus for cardiopulmonary resuscitation with display of the co2 tendency|
    ES18206041T| ES2859563T3|2018-01-11|2018-11-13|Cardiopulmonary resuscitation ventilator with CO2 trend display|
    US16/192,200| US20190209796A1|2018-01-11|2018-11-15|Ventilation apparatus for cardiopulmonary resuscitation with display of the trend in co2|
    CA3024430A| CA3024430A1|2018-01-11|2018-11-15|Ventilation device for cardiopulmonary resuscitation with display of the co2 trend|
    JP2018221290A| JP2019122758A|2018-01-11|2018-11-27|Ventilation device for cardiopulmonary resuscitation comprising display of trend of co2|
    BR102018074807-6A| BR102018074807A2|2018-01-11|2018-11-30|CARDIOPULMONARY RESUSCITATION VENTILATION EQUIPMENT WITH CO2 TREND DISPLAY|
    CN201811532968.3A| CN110025864A|2018-01-11|2018-12-14|Show CO2The air regenerating device for CPR of trend|
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