Cardiopulmonary resuscitation device using chest impedance and automatic external defibrillator fusion system

Abstract

A cardiopulmonary resuscitation device and an automated external defibrillator fusion system using chest impedance according to an embodiment of the present invention includes a support plate for supporting a patient's back, a support base having one end and the other end coupled to both edges of the support plate, a hood coupled to one side of the support base and to which a piston for compressing a chest compression point of the patient is connected, a pair of first electrodes and second electrodes provided on the support plate or the hood for discharging high-voltage energy to apply an electric shock to the patient, an electrocardiogram measurement unit for converting an electrocardiogram signal detected from the patient into a digital signal, a rhythm determination / shock signal generation unit for analyzing the electrocardiogram of the patient using the digital signal and generating an electric shock signal when the electrocardiogram of the patient is a shock-required rhythm, an electric shock unit for converting the electric shock signal into the high-voltage energy and transmitting it to the pair of first and second electrodes, a chest impedance measurement unit for measuring the chest impedance of the patient, and a control unit for raising the piston before analyzing the electrocardiogram of the patient and lowering the piston after analyzing the electrocardiogram of the patient so that chest compression and relaxation are performed, and calculating a profile of an optimal biphasic electric shock waveform during an electric shock using the chest impedance of the patient.

Description

Technical Field

[0001] The present invention relates to a cardiopulmonary resuscitation device and an automated external defibrillator fusion system using chest impedance, and more particularly, to a fusion system for emergency treatment of a patient, comprising a cardiopulmonary resuscitation device and an automated external defibrillator operated based on the chest impedance of the patient.

Background Art

[0002] Cardiopulmonary resuscitation (CPR) is a method of repeating a series of processes such as chest compression, airway maintenance, and artificial respiration. More specifically, when a patient suspected of cardiac arrest occurs, after confirming the safety of the scene and the reaction and breathing status of the fallen person, call for help from the surrounding people and report to the emergency rescue agency as soon as possible. Then, place the heel of the hand and stack both hands, and compress the center of the chest (avoiding the sternum and the center of the nipples) 30 times with the elbows fully extended. The compression depth should be less than 4 - 6 cm. After chest compression, secure the airway and perform artificial respiration 2 times at a rate of 1 time per 1 - 25 seconds while confirming that the chest rises. Alternately perform chest compression and artificial respiration 2 times.

[0003] However, in the case of the general public, even if they have received CPR education, when a cardiac arrest patient occurs, there are problems such as unfamiliarity with CPR, the burden on rib injuries, and the inability to accurately grasp the compression depth because the chest height is not constant for each patient.

[0004] Various types of cardiopulmonary resuscitation (CPR) devices are known. One such device is driven by compressed air or breathing gas (Jolife AB, Lund, Sweden; LucasTM). A unique advantage of the cardiopulmonary resuscitation device is that it is light and portable. Another advantage is the elastic nature of compressed air, which causes the gas-driven cardiopulmonary resuscitation device to cause less damage to the patient's chest than a device equipped with rigid compression means. The known device can be used as emergency equipment in life-saving situations. Also, in the known device, when the patient is admitted to the hospital, the driving gas is supplied from a hospital air supply line suitable for uninterrupted cardiopulmonary resuscitation strikes.

[0005] However, the cardiopulmonary resuscitation device has a problem in that it is difficult to accurately confirm whether the patient's heart has stopped because it is not provided with a function to analyze an electrocardiogram (Electrocardiogram, ECG).

[0006] On the other hand, as a device for analyzing an electrocardiogram, an automated external defibrillator (AED) is known. The automated external defibrillator is a semi-automatic device for removing atrial fibrillation. When it confirms from an electrocardiogram analysis the phenomenon of sudden cardiac arrest (SCA), which is a phenomenon in which the heartbeat is stopped, blood flow to each tissue is interrupted, and the supply of essential substances such as oxygen for biological activities is interrupted, it gives an external electric shock to return the patient's heartbeat to normal.

[0007] However, the automated external defibrillator only provides a cardiac shock based on an electric shock, so it cannot be used for critically ill patients, resulting in a loss of versatility. Also, it is difficult to use for critically ill patients, making it difficult to return the heartbeat to normal. Summary of the Invention Problems to be Solved by the Invention

[0008] An object of the present invention is to analyze an electrocardiogram of a patient during first aid treatment, and based on the electrocardiogram analysis result, perform chest compression and electric shock in parallel or perform chest compression only, so that the patient's heartbeat returns to normal, and to provide a cardiopulmonary resuscitation device using chest impedance and an automatic external defibrillator fusion system.

[0009] Another object of the present invention is to generate a profile of an optimal biphasic (two-phase) electric shock waveform based on the patient's chest impedance, so as to provide the patient with optimal electric shock treatment, and to provide a cardiopulmonary resuscitation device using chest impedance and an automatic external defibrillator fusion system.

[0010] Furthermore, another object of the present invention is to provide the patient with optimal chest compression treatment by sliding a piston for compressing the patient's chest compression point (or compression position) to accurately compress the patient's chest compression point, and to provide a cardiopulmonary resuscitation device using chest impedance and an automatic external defibrillator fusion system.

[0011] However, the technical problems to be achieved by the present invention are not limited to the technical problems mentioned above, and other technical problems not mentioned will be clearly understood by those having ordinary knowledge in the technical field to which the present invention belongs from the following description.

Means for Solving the Problems

[0012] A cardiopulmonary resuscitation device and an automated external defibrillator fusion system using chest impedance according to an embodiment of the present invention for achieving the above object include a support plate for supporting the patient's back, a support base having one end and the other end coupled to both edges of the support plate, a hood coupled to one side of the support base and to which a piston for compressing the patient's chest compression point is connected, a pair of first electrodes and second electrodes provided on the support plate or the hood for discharging high-voltage energy to apply an electric shock to the patient, an electrocardiogram measurement unit for converting an electrocardiogram signal detected from the patient into a digital signal, a rhythm determination / shock signal generation unit for analyzing the electrocardiogram of the patient using the digital signal and generating an electric shock signal when the electrocardiogram of the patient is a shock-required rhythm, an electric shock unit for converting the electric shock signal into the high-voltage energy and transmitting it to the pair of first and second electrodes, a chest impedance measurement unit for measuring the chest impedance of the patient, and a control unit for raising the piston before analyzing the electrocardiogram of the patient and lowering the piston after analyzing the electrocardiogram of the patient so that chest compression and relaxation are performed, and calculating a profile of an optimal biphasic electric shock waveform during the electric shock using the chest impedance of the patient.

Advantages of the Invention

[0013] The present invention provides treatment of chest compression and electric shock to a patient with one system by fusing a cardiopulmonary resuscitation device and an automated external defibrillator, and thus has an effect of excellent versatility as compared with conventional cardiopulmonary resuscitation devices and automated external defibrillators.

[0014] In addition, the present invention can provide optimal electric shock treatment to a patient by generating a profile of an optimal biphasic electric shock waveform based on the chest impedance of the patient.

[0015] Furthermore, the present invention can accurately compress the patient's chest compression point by the sliding of the piston, and thus can provide optimal chest compression treatment to the patient.

[0016] However, the effects obtained from the present invention are not limited to the effects mentioned above, and other effects not mentioned will be clearly understood by those having ordinary knowledge in the technical field to which the present invention pertains from the following description.

Brief Description of the Drawings

[0017]

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Mode for Carrying Out the Invention

[0018] Hereinafter, with reference to the accompanying drawings, embodiments of the present invention will be described in detail so that those having ordinary knowledge in the technical field to which the present invention pertains can easily implement them. However, the description of the present invention is merely an embodiment for structural and functional explanations, and the scope of the rights of the present invention should not be construed as being limited by the embodiments described in the text. That is, since the embodiments can be variously modified and can have various forms, the scope of the rights of the present invention should be understood to include equivalents that can realize the technical idea. In addition, the objects or effects presented in the present invention do not mean that a specific embodiment should include all of them or only such effects, so the scope of the rights of the present invention should not be construed as being limited thereby.

[0019] The meanings of the terms in the present invention are understood as follows.

[0020] Terms such as "first" and "second" are used to distinguish one component from another, and the scope of rights should not be limited by these terms. For example, the first component can be named the second component, and similarly, the second component can also be named the first component. It should be understood that when a component is "connected to" another component, it can be directly connected to the corresponding other component, but there may also be other components in between. In contrast, when a component is "directly connected to" another component, it should be understood that there are no other components in between. On the other hand, other expressions for explaining the relationship between components, namely, "between" and "immediately between", or "adjacent to" and "directly adjacent to", etc., should also be analyzed in the same way.

[0021] Singular expressions include plural expressions unless the context clearly indicates otherwise. Also, terms such as "including" or "having" are intended to specify the existence of the recited features, numbers, steps, operations, components, parts, or combinations thereof, and should be understood not to exclude the existence or possibility of addition of one or more other features, numbers, steps, operations, components, parts, or combinations thereof.

[0022] All terms used herein have the same meaning as commonly understood by those of ordinary skill in the art to which the present invention pertains, unless otherwise defined. Terms defined in commonly used dictionaries should be construed to be consistent with the meaning they have in the context of the relevant art, and should not be construed to have an ideal or overly formal meaning unless clearly defined in the present invention.

[0023] FIG. 1 is a perspective view of a partial configuration of a cardiopulmonary resuscitation device using chest impedance and an automatic external defibrillator fusion system according to an embodiment of the present invention, FIG. 2 is a schematic diagram of a partial configuration of the cardiopulmonary resuscitation device using chest impedance and the automatic external defibrillator fusion system in FIG. 1, and FIG. 3 is a block diagram showing a unit provided in a hood according to an embodiment of the present invention.

[0024] As shown in FIGS. 1 to 3, a cardiopulmonary resuscitation device using chest impedance and an automatic external defibrillator fusion system (hereinafter referred to as "fusion system") according to an embodiment of the present invention includes a support plate 100, a support base 200, and a hood 300.

[0025] The support plate 100 is formed in a shape for supporting the back of a patient with diseases such as sudden cardiac arrest and ventricular fibrillation, and includes a sliding guide 110 for sliding a support base 200 and a hood 300 having a shape in which a cardiopulmonary resuscitation device and an automatic external defibrillator are integrated, a stopper 120 for fixing the positions of the support base 200 and the hood 300, and a band 130 for wrapping the upper part of the patient's arm including the elbow to fix the patient's arm.

[0026] The support plate 100 is provided with an internal space on the side where a frame 115 provided on the sliding guide 110 can be retracted for adjusting the height of the piston 310.

[0027] The sliding guide 110 is provided at both edges of the support plate 100, and one end and the other end of the support base 200 are slidably coupled so that the support base 200 can slide forward or backward.

[0028] As shown in FIG. 2(b) in which the A region in FIG. 2(a) is enlarged, the sliding guide 110 is provided with a frame 115 that can be retracted into the support plate 100 or pulled out from the inside of the support plate 100, so that the distance between both ends of the support base 200 can be adjusted, and thereby the height of the piston 310 can be adjusted.

[0029] Here, adjusting the height of the piston 310 is to prevent a situation where the chest compression point of a specific patient cannot be compressed in the piston 310 because each patient has a different body shape.

[0030] The stopper 120 is provided on the sliding guide 110 and has a shape that can be bound to one end and the other end of the support base 200. Thus, it is bound to one end and the other end of the support base 200, and the positions of the support base 200 and the hood 300 are fixed from the binding to one end and the other end of the support base 200.

[0031] As shown in FIGS. 8 and 9, the band 130 has its back supported by the support plate 100, wraps around the upper part of the arm including the patient's elbow during chest compression, and is provided with a cuff 131 for fixing the patient's arm (D).

[0032] The cuff 131 includes a D-ring 132 and an opening 133. With a structure that passes through the D-ring 132, on the inner surface, it wraps around the patient's arm (D), is in close contact with the patient's arm (D), and hook-and-loop fasteners 131a, 131b that are detachable from each other are provided on one side so that the wrapped state of the patient's arm (D) is maintained.

[0033] Although not shown, such a cuff 131 is wound around a shaft formed at the lower part of the support plate 100, is connected to the support plate 100, and is preferably arranged in a pair on the side part of the support plate 100 so as to wrap around all of a pair of patients' arms (D).

[0034] In addition, the cuff 131 is formed with an opening 133 having a diameter into which the user's hand can be inserted so that the user can grip the support plate 100 and the cuff 131 simultaneously. The user inserts their hand into the groove formed at the lower part of the support plate 100 where the shaft of the support plate 100 (not shown) is provided together with the opening 133, and thus can grip the support plate 100 to which the cuff 131 is connected and move the fusion system to a desired location.

[0035] On the other hand, although the fusion system of FIG. 9 does not include the support plate 100 for supporting the patient's back, it is desirable to understand that it is a fusion system according to an embodiment of the present invention including the support plate 100.

[0036] The support base 200 is coupled to the sliding guide 110 such that the lower end of the piston 310 moves to a position pressing the patient's chest compression point. In one embodiment of the present invention, the shape for supporting the hood 300 is arched, but is not limited thereto.

[0037] One end and the other end of the support base 200 are movably coupled to a pair of sliding guides 110, so that the support base 200 slides forward or backward about the sliding guide 110, or the distance between both ends can be adjusted by retracting and extending the frame 115.

[0038] It is desirable to perform the forward and backward sliding of the support base 200 and the distance adjustment between both ends before the piston 310 presses the patient's chest compression point. When the support base 200 moves to a position for the piston 310 to press and relax the patient's chest compression point, one end and the other end are bound by a pair of stoppers 120.

[0039] The support base 200 is configured such that one end and the other end are detachable from a pair of sliding guides 110, is detachable from the pair of sliding guides 110, and is detachable from the support plate 100 together with the hood 300 by detachment, and can be used as another device.

[0040] The hood 300 is coupled to one side of the support base 200, more specifically, to the center portion (Arch Crown) of the arched support base 200, and is connected to the piston 310 for pressing the patient's chest compression point. The components of the hood 300 are as follows.

[0041] As shown in FIG. 3, the hood 300 includes the piston 310, a control unit 320, an electrocardiogram measurement unit 330, a rhythm determination / shock signal generation unit 340, an electric shock unit 350, and a chest impedance measurement unit 360. The components are either exposed to the outside or provided within the hood 300.

[0042] Before compressing the patient's chest compression point, the piston 310 is in a state separated from the patient's chest and is operated by the control unit 320 to compress and then separate from the patient's chest compression point, repeating the process of relaxing the patient's chest compression point.

[0043] The piston 310 operates based on a continuous compression mode in which the piston continuously compresses and relaxes the patient's chest according to a chest compression mode set by the control unit 320, or a compression 30:2 mode in which after 30 compressions of the patient's chest, 2 artificial breaths are performed and the patient's chest compression and artificial respiration are parallel, providing chest compression-based first aid to the patient.

[0044] The piston 310 is operated by the control unit 320 to intersect or operate simultaneously with the electric shock unit 350, providing cardiopulmonary resuscitation and electric shock-based first aid to the patient.

[0045] Also, the piston 310 can directly compress the patient's chest compression point, but is not limited thereto. A cap for directly compressing the patient's chest compression point is detachable at the lower end, and the cap can be made of a material such as silicon for relaxing the impact during the process of compressing the patient's chest compression point.

[0046] That is, the hood 300 couples the piston 310 or a cap 700 to the lower end of the piston 310, and compresses the patient's chest compression point with the cap to perform cardiopulmonary resuscitation. In an embodiment of the present invention, the lower end of the piston 310 compresses the patient's chest compression point to explain the fusion system of the present invention in detail.

[0047] On the one hand, according to the operating timing of the piston 310 and the electric shock unit 350, the fusion system of the present invention can provide chest compression and electric shock to the patient alternately or simultaneously by one system. Therefore, compared with the conventional cardiopulmonary resuscitation device and the automated external defibrillator, it has an excellent effect in versatility.

[0048] The control unit 320 can control the operations of the piston 310, the electrocardiogram measurement unit 330, the rhythm determination / shock signal generation unit 340, the electric shock unit 350, and the chest impedance measurement unit 360, which are components provided in the hood 300, and a plurality of buttons are provided for this purpose.

[0049] Although not shown, as a specific example, the plurality of buttons may include a power button for turning on / off the power of the fusion system, a control button for setting the mode of the fusion system to the automatic cardiac shock mode and / or the chest compression mode, a stop button for stopping the operation of the piston 310, a compression mode setting button for causing the piston 310 to perform chest compression (CPR) on the patient or setting the chest compression mode of the piston 310, a compression depth setting button for setting the chest compression depth (depth) of the piston 310, a compression frequency setting button for setting the number of chest compressions of the piston 310, a shock button for operating the electrocardiogram measurement unit 330, the rhythm determination / shock signal generation unit 340, and the electric shock unit 350, and an adaptive length change button for selecting whether to correct the update of the chest compression start position of the patient and the disappearance of the chest compression depth.

[0050] When an input signal is input to the power button and the power of the fusion system is turned on, the control unit 320 performs a self test to determine whether initialization and normal operation are possible. When the fusion system is on, if an input signal is input to the power button again, the initialization is set and the power of the fusion system is turned off.

[0051] When the chest compression mode set by the compression mode setting button is the compression continuous mode, the control unit 320 controls the operation of the piston 310 so that the compression and relaxation of the patient's chest are repeated. On the contrary, when the chest compression mode set by the compression mode setting button is the compression 30:2 mode, the operation of the piston 310 can be controlled so that after the patient's chest is compressed 30 times, two artificial breaths are performed.

[0052] When an input signal is input to the compression depth setting button, the control unit 320 can control the operation of the piston 310 so that the patient's chest is compressed at at least one depth of 4 cm, 4.5 cm, 5 cm, or 5.5 cm. Furthermore, when an input signal is input to the compression depth setting button in the initialization state, the patient's chest is compressed by 5 cm. When a signal is input thereafter, the patient's chest is compressed by 5.5 cm. When a signal is input again, the patient's chest is compressed by 4 cm. When a signal is input further, the operation of the piston 310 can be controlled so that the patient's chest is compressed by 4.5 cm.

[0053] When an input signal is input to the compression frequency setting button, the control unit 320 can control the operation of the piston 310 so that the patient's chest is compressed at at least one frequency of 100 times, 110 times, or 120 times per minute. Furthermore, when an input signal is input to the compression frequency setting button in the initialization state, the patient's chest is compressed 110 times. When a signal is input again, the patient's chest is compressed 120 times. When a signal is input further, the operation of the piston 310 can be controlled so that the patient's chest is compressed 100 times.

[0054] The electrocardiogram measurement unit 330 is connected to the rhythm determination / shock signal generation unit 340 and the control unit 320. When operated by the control unit 320, after detecting an electrocardiogram signal from the patient, it amplifies the signal, removes the noise of the amplified electrocardiogram signal, converts the electrocardiogram signal into a digital signal, and transmits it to the rhythm determination / shock signal generation unit 340.

[0055] When an analog electrocardiogram signal is detected, the electrocardiogram measurement unit 330 is provided with an amplifier for amplifying the signal, a filter for removing noise from the electrocardiogram signal amplified by the amplifier, and an A / D converter for converting the electrocardiogram signal from which noise has been removed by the filter into a digital signal.

[0056] The electrocardiogram measurement unit 330 is provided on one side of the hood 300 to detect an analog electrocardiogram signal from a patient, and is composed of electrodes or pads that can be attached to the patient, so as to detect an electrocardiogram signal from the patient who supports the back on the support plate 100.

[0057] Here, the process of detecting the electrocardiogram signal of the patient by the electrodes or pads is a normal matter, so the description thereof is omitted for convenience.

[0058] The rhythm determination / shock signal generation unit 340 is built into the hood 300 and is connected to the electrocardiogram measurement unit 330 so as to operate together when the electrocardiogram measurement unit 330 is operated by the control unit 320, thereby receiving a digital signal from the electrocardiogram measurement unit 330.

[0059] When the rhythm determination / shock signal generation unit 340 receives a digital signal from the electrocardiogram measurement unit 330, it analyzes the electrocardiogram of the patient with the digital signal to determine whether the electrocardiogram of the patient is a shockable rhythm or a nonshockable rhythm. When it is determined that the electrocardiogram of the patient is a shockable rhythm, an electrical shock signal is generated, and when the electrical shock unit 350 operates, the electrical shock signal is transmitted to the electrical shock unit 350.

[0060] The electrical shock unit 350 is connected to the rhythm determination / shock signal generation unit 340, and when it is determined from the rhythm determination / shock signal generation unit 340 that the electrocardiogram of the patient is a shockable rhythm, it receives an electrical shock signal from the rhythm determination / shock signal generation unit 340 when operating by the control unit 320.

[0061] When the electric shock unit 350 receives an electric shock signal, it releases higher voltage energy than a pair of first electrodes 351 and a pair of second electrodes 352, so that an electric shock is applied to the patient.

[0062] The pair of first and second electrodes 351 and 352 are preferably attached to the patient's chest so that an electric shock is applied to the patient. Specifically, the pair of first electrodes 351 can be attached under the patient's right collarbone to apply an electric shock to the patient, and the pair of second electrodes 352 can be attached to the side adjacent to the patient's left nipple to apply an electric shock to the patient.

[0063] Also, the pair of first and second electrodes 351 and 352 are electrically connected to the electric shock unit 350 through a cable by detaching from and attaching to the electric shock unit 350, and can release higher voltage energy.

[0064] Also, the pair of first and second electrodes 351 and 352 are described as components of the hood 300 in one embodiment of the present invention, but are not limited thereto. As components provided on the support plate 100, they can be electrically connected to the electric shock unit 350 through a cable and release higher voltage energy.

[0065] The chest impedance measurement unit 360 measures the patient's chest impedance and does not limit the method of measuring the chest impedance. As a specific example, using a pair of first electrodes 351 which are current output electrodes capable of not only releasing higher voltage energy but also outputting current, and a pair of second electrodes 352 which are voltage detection electrodes capable of voltage detection, the chest impedance values during compression and relaxation of the patient's chest can be continuously measured.

[0066] On the one hand, the control unit 320 calculates whether a pair of first and second electrodes 351 and 352 are properly attached to the patient within the patient's chest impedance range measured by the chest impedance measurement unit 360, and calculates the profile of the biphasic electric shock waveform using the chest impedance value 421a when the patient's chest is compressed and the chest impedance value 421b when the patient's chest is relaxed.

[0067] In one embodiment of the present invention, the fusion system further includes a storage unit 400 for storing information necessary during the emergency treatment process of the patient. The storage unit 400 consists of a first storage unit 410 and a second storage unit 420, and the information stored in each storage unit 410 and 420 is as follows.

[0068] FIG. 4 is a diagram showing a storage unit provided in a cardiopulmonary resuscitation device using chest impedance and an automatic external defibrillator fusion system according to an embodiment of the present invention and the stored information.

[0069] As shown in FIG. 4, the first storage unit 410 already stores start time information 411 for starting the electrocardiogram analysis of the patient, end time information 412 for ending the electrocardiogram analysis of the patient, and chest compression start position information 413 for causing the piston 310 to return after completing the chest compression and relaxation of the patient.

[0070] The second storage unit 420 stores the chest impedance value 421a when the patient's chest is compressed measured by the chest impedance measurement unit 360 and its average value, the chest impedance value 421b when the patient's chest is relaxed and its average value, compression time information 422 for the piston 310 to compress the patient's chest compression point, and relaxation time information 423 for relaxing the patient's chest compression point.

[0071] Although the storage unit 400 has been described as including a first storage unit 410 and a second storage unit 420 in one embodiment, it is not limited thereto. The first storage unit 410 and the second storage unit 420 may be provided as one storage unit, and each piece of information may be stored or already stored therein.

[0072] On the other hand, the control unit 320 calculates the average values of the chest impedance during chest compression and relaxation of the patient using the compression time information and relaxation time information stored in the second storage unit 420, respectively, and can generate profiles of the optimal biphasic electric shock waveforms during chest compression and relaxation of the patient based on the respective average values of the chest impedance.

[0073] In addition, when fluctuations occur in the chest impedance values 421a and 421b during chest compression and relaxation of the patient stored in the second storage unit 420, the control unit 320 calculates the absolute values of the differences between the respective chest impedance values 421a and 421b during chest compression and relaxation of the patient continuously measured by the chest impedance measurement unit 360 and the average values of a certain number of chest impedance values of the chest impedance values 421a and 421b stored in the second storage unit 420.

[0074] In addition, when the calculated average value of the chest impedance and the absolute value of the difference are equal to or greater than a predetermined absolute value, the control unit 320 excludes the average value of the chest impedance before the occurrence of the fluctuation stored in the second storage unit 420, and after excluding the average value of the chest impedance, replaces it with the chest impedance values 421a and 421b during chest compression and relaxation of the patient measured by the chest impedance measurement unit 360, and can generate profiles of the optimal biphasic electric shock waveforms during chest compression and relaxation of the patient using the chest impedance values 421a and 421b.

[0075] That is, according to one embodiment, the chest impedance value 421a during chest compression and the chest impedance value 421b during chest relaxation are obtained respectively, and the average value of each is calculated. When chest compression is performed at the time of applying an electric shock using the calculated average chest impedance values, a profile of the electric shock waveform corresponding to the average impedance value during chest compression is generated. When chest relaxation is performed at the time of applying an electric shock, a profile of the electric shock waveform corresponding to the average impedance value during chest relaxation is generated, so that an optimal electric shock waveform profile for the patient is generated.

[0076] Here, the profile of the optimal biphasic electric shock waveform generated by the control unit 320 will be described in detail with reference to FIG. 7 and Table 1 below.

[0077]

Table 1

[0078] As shown in FIG. 7, the profile of the biphasic electric shock waveform includes a positive waveform and a negative waveform, and indicates the current value and duration applied when an electric shock is applied to the patient. Further, in Table 1, the duration (ms) of the first phase interval, the duration (ms) of the second phase interval, the peak current (A), and the discharge energy (J) calculated therefrom provided by the average impedance value measured during chest relaxation or contraction of the patient are shown. The discharge energy (J) in Table 1 is the discharge energy for adult patients. Desirably, 200 J can be applied to adult patients and 150 J can be applied to pediatric patients, but it is not limited thereto.

[0079] Referring to FIG. 7 again, the profile of the biphasic electric shock waveform has the duration (ms) on the x-axis and the current (A) on the y-axis. FIG. 7 shows a symmetric profile according to one embodiment of the present invention, but it is not limited thereto, and an asymmetric profile may be used.

[0080] In actually implementing the present invention, the duration (ms) of the first phase interval, the duration (ms) of the second phase time, and the peak current (A) value according to each impedance value shown in Table 1 above are the duration (ms) of the first phase interval, the duration (ms) of the second phase time, and the peak current (A) value corresponding to the average impedance value measured during chest compression and relaxation at a predetermined value in the control unit 320. According to the biphasic electric shock waveform profile, an electric shock will be applied to the patient.

[0081] In FIG. 7, a is the current value before the first phase interval, b is the current value between the first phase interval and the second phase interval, c is the current value after the second phase interval, and the values of a, b, and c can all be the same. Also, α is the reduced amount of decrease while the peak current decreases in the first phase interval, β is the reduced amount of decrease when the peak current decreases in the second phase interval, and the values of α and β can be the same as each other. Also, A is the duration in the first phase interval, B is the duration in the second phase interval, and the values of A and B can be the same. Also, the circled number 1 is the difference value between the current value immediately before the end of the first phase interval and the current value immediately before the start of the second phase interval, the circled number 2 is the absolute value of the peak current in the first phase interval, and the sum of the circled number 1 and α can be the circled number 2.

[0082] In one embodiment of the present invention, the fusion system further includes a sensor 500 for sensing information during the emergency treatment process of the patient, and the sensor 500 can consist of a first sensing sensor 520 and a second sensing sensor 530.

[0083] FIG. 5 is a diagram showing the sensor provided in the cardiopulmonary resuscitation device using chest impedance and the automatic external defibrillator fusion system according to one embodiment of the present invention.

[0084] As shown in FIG. 5, the sensor 500 senses the current position of the piston 310 in real time by the first sensing sensor 520 and the second sensing sensor 530 to generate current position information, and transmits the current position information of the piston 310 to the control unit 320 in real time.

[0085] On the other hand, before analyzing the electrocardiogram of the patient, the control unit 320 will control the operation of the piston 310 using the information of the first sensing sensor 520 and the second sensing sensor 530. An example of the process of controlling the operation of the piston 310 using the current position information of the piston 310 is as follows.

[0086] Before analyzing the electrocardiogram of the patient, the control unit 320 moves the lower end of the piston 310 to the chest compression start position so that the lower end of the piston 310 does not contact the patient's chest. When the lower end of the piston 310 moves to the chest compression start position, it determines whether the current position information of the piston 310 received in real time matches the chest compression start position, and by arranging the lower end of the piston 310 to be relatively above the chest compression start position, the piston 310 is in a standby state before compressing the patient's chest compression point.

[0087] In addition, after analyzing the electrocardiogram of the patient, the control unit 320 can control the operation of the piston 310 so that the patient's chest is compressed and relaxed according to the settings of the chest compression mode, chest compression depth, and chest compression times by a plurality of buttons from the chest compression start position.

[0088] Also, before the piston 310 compresses and relaxes the patient's chest compression point, when the piston 310 descends by the chest compression depth set by the compression depth setting button, the control unit 320 makes the patient's chest be compressed, so that the interval between the lower end of the piston 310 and the patient's chest becomes a predetermined interval (0 - 2 cm). That is, the chest compression start position of the patient means the position of the piston 310 that should be arranged for the patient's chest compression during the patient's chest compression and relaxation process.

[0089] In addition, the optimization of the patient's chest compression start position by the control unit 320 is performed, in one embodiment, by updating the patient's chest compression start position every certain period (2 minutes and 30 seconds after the chest compression mode, chest compression depth, and chest compression frequency are set). Updating the patient's chest compression start position every such certain period is because the chest may sink due to the patient's chest compression and relaxation, or the patient may move during the process of the patient supporting their back on the support plate 100, and the optimization of the patient's chest compression start position may not be achieved.

[0090] In addition, the control unit 320 can receive electrical information (e.g., power) used from the motor for driving the piston 310 and the current position information of the piston, and update the patient's chest compression start position when a change in the patient's chest compression start position is detected. Here, the sensors for sensing electrical information, the rotation speed of the motor, and the piston movement distance information can be the first sensing sensor 520 and the second sensing sensor 530.

[0091] Referring to FIG. 5 again, the first sensing sensor 520 can sense the electrical information used from the motor and transmit the electrical information to the control unit 320.

[0092] Such a first sensing sensor 520 is provided in the drive circuit of the motor, and after grasping the position of the lower end of the piston 310, it is transmitted to the control unit 320 in real time.

[0093] Here, the control unit 320 can receive the lower end position value of the piston 310 from the first sensing sensor 520 and determine the current position of the piston 310. Here, as described above, when the cap 700 is coupled to the lower end of the piston 310 to compress the patient's chest, the control unit 320 can calculate the lower end position value of the piston 310 in consideration of the value of the predetermined width of the first housing 710 located between the patient's chests.

[0094] As an example of a method for the first sensing sensor 520 to grasp the position of the lower end of the piston, when the piston 310 descends due to the rotation of the motor, during the descent of the void, the power consumption of the motor is maintained constant. During the descent of the space, the power consumption of the motor is constant, and the power consumption by the motor will increase from the moment the lower end of the piston touches the chest surface of the patient. The first sensing sensor 520 senses the power consumption by the motor, recognizes the moment when the power consumption increases as the chest surface of the patient, and here, can grasp the position value of the lower end of the piston and transmit it to the control unit 320.

[0095] Also, when the lower end of the piston 310 contacts the chest surface of the patient at regular intervals, the first sensing sensor 520 uses the difference in electrical information to sense whether the chest shape of the patient can be changed, and transmits whether the chest shape of the patient can be changed to the control unit 320.

[0096] The second sensing sensor 530 is provided on the motor. After sensing the rotation speed of the motor and the moving distance of the piston, it generates moving distance information of the piston 310 and transmits the moving distance information of the piston to the control unit 320.

[0097] In one embodiment, the sensor 500 includes the first sensing sensor 520 and the second sensing sensor 530, but is not limited thereto. The first sensing sensor 520 and the second sensing sensor 530 are provided as one sensing sensor to sense changes in electrical information, the rotation speed of the motor, and the moving distance information of the piston.

[0098] In one embodiment of the present invention, the fusion system further includes a notification unit 600 to notify the user of a voice message for the progress of the emergency treatment of the patient. The notification unit 600 includes a first notification unit 610 and a second notification unit 620.

[0099] FIG. 6 is a diagram showing a notification unit provided in a cardiopulmonary resuscitation device using chest impedance and an automatic external defibrillator fusion system according to an embodiment of the present invention.

[0100] As shown in FIG. 6, when the chest compression start position of the patient is updated, the first notification unit 610 outputs a first message for notifying that the chest compression start position of the patient has been updated, and a second message for notifying a difference value between the existing patient's chest compression start position before the update and the updated patient's chest compression start position.

[0101] Further, when the difference value between the existing patient's chest compression start position and the updated patient's chest compression start position is equal to or greater than a specific critical value, the first notification unit 610 outputs a third message. The specific critical value that is the criterion for outputting the third message is not limited, but in one embodiment of the present invention, it can be set to 1 cm.

[0102] That is, in one embodiment, the first notification unit 610 can output a third message when the difference value between the existing patient's chest compression start position and the updated patient's chest compression start position is 1 cm or more. When the chest compression start position of the patient is updated, a fourth message for requesting the user to select the chest compression depth (at least one of 4 cm, 4.5 cm, 5 cm, 5.5 cm) and the number of chest compressions (at least one of 100 times, 110 times, 120 times per minute) of the piston 310 can be output.

[0103] Here, after being provided with the fourth message, the user of the fusion system for first aid treatment of the patient can input signals to the compression depth setting button and the compression number setting button of the control unit 320 so that the chest compression depth and the number of chest compressions of the piston 310 are selected, and the control unit 320 can update the chest compression depth and the number of chest compressions when the chest compression depth and the number of chest compressions are selected by the compression depth setting button and the compression number setting button.

[0104] In addition, when the first notification unit 610 senses a change in the patient's chest shape from the first sensing sensor 520, it can output a fifth message for notifying the user that the patient's chest shape has changed.

[0105] In the fusion system according to an embodiment of the present invention, when at least one of the first to fifth messages output from the first notification unit 610, which is an auditory display device, is output as sound, an LED implemented by an LED electronic display board or an LED blinking light and a visual display device provided with a display can visually output the same message as the message output from the first notification unit 610 and provide it to the user.

[0106] When the absolute value of the difference between the chest impedance value calculated at the current time and the average chest impedance values during chest compression and relaxation of the patient stored in the second storage unit 420 by the control unit 320 is a value equal to or greater than a predetermined absolute value, the second notification unit 620 can output a message including sound and visual expression to notify the user.

[0107] On the other hand, the cap 700 attached to the lower end of the piston 310 is attached to the lower end of the piston 310 and is made of a member having a different hardness from the hard piston 310, so that it can continuously provide a buffering action for relaxing and distributing the pressure acting on the patient's chest.

[0108] Hereinafter, the structure of the cap 700 will be described in detail.

[0109] FIG. 10 is a perspective view of a cap according to an embodiment of the present invention, FIG. 11 is a cross-sectional view taken along line A-A in FIG. 10, FIG. 12 is a perspective view showing a first member according to an embodiment of the present invention, FIG. 13 is a plan view showing the first member according to an embodiment of the present invention, and FIG. 14 is a cross-sectional view taken along line B-B in FIG. 13.

[0110] As shown in FIGS. 10 to 14, the cap 700 includes a first member 710 and a second member 720.

[0111] After the piston 310 and the cap 700 are fitted, when the piston 310 expands toward the patient's chest, the first member 710 can directly contact the chest compression point of the patient to compress the patient's chest.

[0112] Further, the first member 710 is made of at least one of ethylene vinyl acetate, polyethylene, polyethylene - polypropylene blend, polystyrene, neoprene, chloroprene, polyurethane and biocompatible silicone. Due to the characteristics of such materials, it can be embodied in a form that adapts to the shape of the patient's chest.

[0113] Furthermore, among the first member 710, the biocompatible silicone has a Shore A hardness of 10 to 30, and the other materials have an Asker C hardness of 10 to 20. In an embodiment of the present invention, the Asker C hardness is measured by an Asker hardness tester that measures the hardness based on the depth at which a push pin of a predetermined shape is pressed into the surface of the sample by the force of a spring and the balance state where the resistance of the sample and the force of the spring are balanced. The shore hardness is measured by measuring the height of the rebound when a falling object with a small diamond fixed at its end is dropped from a certain height.

[0114] Also, as shown in FIGS. 11 to 14, the first member 710 has an outer shape formed by a first housing 711, and the first housing 711 is provided with a plurality of air flow ports 712 and a seating portion 713.

[0115] The first housing 711 is composed of an integrally formed inner housing 711a and an outer housing 711b, and the lower surface will contact the patient's chest.

[0116] When pressure is transmitted from the patient's chest to the lower surface during the patient's chest compression process, a plurality of air flow ports 712 are formed on the lower surface of the internal housing 711a so that a volume change occurs due to the air flow in the gap space (A).

[0117] The gap space (A) between the upper side of the internal housing 711a and the bottom 723 can have its volume decreased when air flows out to the outside along the air flow ports 712 by the piston 310 that expands during the patient's chest compression process. On the contrary, when the chest compression of the patient ends and the device moves away from the patient's chest, the volume can be increased by the air flowing in through the air flow ports 712.

[0118] During the patient's chest compression process, the lower surface of the internal housing 711a contacts the patient's chest. Due to the expansion of the piston 310, air flows out from the gap space (A) to the outside, and the volume of the gap space (A) decreases. When the seating portion 713 provided at the center contacts the lower surface of the bottom 723, a negative pressure is generated in the gap space (A). After the negative pressure is generated in the gap space (A), when the piston 310 contracts, the lower surface that contacts the patient's chest compression point can pull the patient's chest and move upward.

[0119] A protruding member insertion port 7110 into which a protruding member 7230 described later can be fitted is formed at the boundary between the internal housing 711a and the external housing 711b of the first housing 711.

[0120] The protruding member insertion port 7110 is formed in a circular shape at the boundary between the internal housing 711a and the external housing 711b so that the protruding member 7230 can be fitted.

[0121] Also, the internal housing 711a and the external housing 711b are configured such that the side walls forming the protruding member insertion port 7110 protrude upward, so that a gap space (A) is generated between the internal housing 711a and the bottom 723 in the fitting structure of the first member 710 and the second member 720.

[0122] When the first housing 711 compresses the patient's chest, it needs to adapt to the patient's chest. Thus, the lower surface of the inner housing 711a that contacts the patient's chest compression point is preferably made of biocompatible silicon that is easy to adapt to the patient's chest among applicable materials. By continuously providing a buffering effect that relaxes and distributes the pressure acting on the patient's chest, it is possible to prevent rib fractures and hemothorax from occurring during the first aid process.

[0123] Also, when air in the gap space (A) flows out to the outside through a plurality of air flow ports 712 of the first housing 711, and the volume of the gap space (A) decreases, and the landing part 713 contacts the lower surface of the bottom part 723 of the second member 720, the gap space (A) is set to a negative pressure state.

[0124] Furthermore, the first housing 711 is configured such that the inner housing 711a and the outer housing 711b are bellows-shaped so that the volume of the gap space (A) can change due to air flow.

[0125] The second member 720 is fitted with the piston 310 and comes into contact with the lower end of the piston 310, and is fitted to the first member 710.

[0126] Such a second member 720 can be made of one of polyurethane and polypropylene and biocompatible silicon, so that the material can be different from that of the first member 710.

[0127] Also, when the second member 720 is made of biocompatible silicon, it has a Shore A hardness of 40 to 60, and when made of other materials, it has an Asker C hardness of 25 to 30, so that the hardness can be different from that of the first member 710.

[0128] Also, as shown in FIGS. 9 to 12, the second member 720 has a second housing 721, a piston fitting portion 722, and a bottom portion 723 integrally formed.

[0129] The second housing 721 forms the outer shape of the second member 720 and is integrally formed with the piston fitting portion 722 and the bottom portion 723.

[0130] The piston fitting portion 722 is integrally formed with the second housing 721 and forms a piston fitting port 7220 so that the piston 310 fits on the upper part of the second member 720.

[0131] Further, the piston fitting portion 722 is a portion provided in a state bent from the second housing 721 to form a piston fitting port 7220 into which a fastening member (not shown) of the piston 310 can be retracted, and includes a first piston fitting portion 722a, a second piston fitting portion 722b, a third piston fitting portion 722c, and a fourth piston fitting portion 722d.

[0132] Furthermore, a pair of grooves 724a and 724b are formed between the first piston fitting portion 722a and the second piston fitting portion 722b, and between the third piston fitting portion 722c and the fourth piston fitting portion 722d. When the piston 310 fits into the piston fitting port 7220, a fastening member formed on a part of the outer peripheral surface of the piston 310 is retracted into the grooves 724a and 724b.

[0133] That is, the lower end of the piston 310 contacts the bottom portion 723, and the fastening member is retracted into the pair of grooves 724a and 724b, whereby the piston 310 is fastened to the cap 700.

[0134] Also, in the process of engaging and disengaging the fastening member of the piston 310 with the grooves 724a and 724b, the lower part of the piston fitting portion 722 can be expanded (or, flow) to the outside of the second housing 721 so that the fastening member of the piston 310 is retracted or pulled out from the pair of grooves 724a and 724b. Thereby, an expansion space 7221 is formed in the gap space with the second housing 721.

[0135] The bottom portion 723 is the lower surface of the second member 720, which is integrally formed with the second housing 721. When the piston 310 is fitted into the piston fitting opening 7220, the upper surface will come into contact with the lower end portion of the piston 310.

[0136] Further, a protruding member 7230 is provided on the lower surface of the bottom portion 723 and is fitted into the protruding member insertion opening 7110, thereby realizing the fitting of the first member 710 and the second member 720.

[0137] The protruding member 7230 can protrude circularly from the lower surface of the bottom portion 723 so as to be fitted into the protruding member insertion opening 7110.

[0138] As described above, a detailed description of the preferred embodiments of the present invention is provided so that those skilled in the art can embody and implement the present invention. In the foregoing, the preferred embodiments of the present invention have been described with reference thereto. However, those skilled in the art in the relevant technical field will understand that the present invention can be variously modified and changed without departing from the scope of the present invention. For example, those skilled in the art can utilize the respective configurations described in the above-described embodiments in a manner of combining them with each other. Therefore, the present invention is not intended to be limited to the embodiments appearing herein, but is intended to be given the broadest scope consistent with the principles and novel features disclosed herein.

[0139] The present invention can be embodied in other specific forms without departing from the spirit and essential features of the present invention. Therefore, the above detailed description should not be analyzed restrictively in all aspects and should be considered exemplary. The scope of the present invention is determined by a reasonable analysis of the appended claims, and all changes within the equivalent scope of the present invention are included in the scope of the present invention. The present invention is not intended to be limited to the embodiments appearing herein, but is intended to be given the broadest scope consistent with the principles and novel features disclosed herein. Also, claims that do not have an explicit citation relationship in the claims can be combined to form embodiments or included as new claims by amendment after filing.

Industrial Applicability

[0140] The cardiopulmonary resuscitation device and the automated external defibrillator fusion system using chest impedance according to the present invention can provide treatment of chest compression and electric shock to a patient with one system by fusing a cardiopulmonary resuscitation device and an automated external defibrillator. Therefore, compared with conventional cardiopulmonary resuscitation devices and automated external defibrillators, it has excellent versatility and thus has industrial applicability.

[0141] In addition, the cardiopulmonary resuscitation device and the automated external defibrillator fusion system using chest impedance according to the present invention can generate a profile of an optimal biphasic electric shock waveform based on the chest impedance of the patient, and thus can provide optimal electric shock treatment to the patient, so it has industrial applicability.

[0142] Furthermore, the cardiopulmonary resuscitation device and the automated external defibrillator fusion system using chest impedance according to the present invention can accurately compress the chest compression point of the patient by the sliding of the piston, and thus can provide optimal chest compression treatment to the patient, so it has industrial applicability.

Claims

1. A support plate for supporting a patient's back, a support base with one end and the other end coupled to both edges of the support plate, a hood coupled to one side of the support base and to which a piston for compressing a chest compression point of the patient is connected, a pair of first electrodes and second electrodes provided on the support plate or the hood for discharging high-voltage energy to apply an electric shock to the patient, an electrocardiogram measurement unit for converting an electrocardiogram signal detected from the patient into a digital signal, a rhythm determination / shock signal generation unit for analyzing the electrocardiogram of the patient using the digital signal and generating an electric shock signal when the electrocardiogram of the patient is a shock-required rhythm, an electric shock unit for converting the electric shock signal into the high-voltage energy and then transmitting it to the pair of first and second electrodes, a chest impedance measurement unit for measuring the chest impedance of the patient, and a control unit for causing the piston to rise before analyzing the electrocardiogram of the patient and causing the piston to descend after analyzing the electrocardiogram of the patient so that chest compression and relaxation are performed, and for calculating a profile of an optimal biphasic electric shock waveform during an electric shock using the chest impedance of the patient. A cardiopulmonary resuscitation device using chest impedance and an automated external defibrillator fusion system characterized by including the above.

2. The cardiopulmonary resuscitation device using chest impedance and the automated external defibrillator fusion system according to claim 1, wherein the chest impedance measurement unit continuously measures chest impedance values during chest compression and relaxation of the patient using the pair of first electrodes and second electrodes.

3. The cardiopulmonary resuscitation device using chest impedance and the automated external defibrillator fusion system according to claim 2, wherein the control unit calculates whether the pair of first and second electrodes are properly attached to the patient within the chest impedance range of the patient, and calculates a profile of a biphasic electric shock waveform using chest impedance values during chest compression and relaxation of the patient.

4. The cardiopulmonary resuscitation device and automated external defibrillator fusion system using chest impedance according to claim 3, characterized in that it includes a second storage unit for storing each chest impedance value measured by the chest impedance measurement unit when the patient's chest is compressed and relaxed, the compression time information of the piston compressing the chest compression point of the patient, and the relaxation time information for relaxing the chest compression point of the patient.

5. The control unit calculates the average chest impedance values when the patient's chest is compressed and relaxed using the compression time information and the relaxation time information, and generates an optimal biphasic electric shock waveform profile when the patient's chest is compressed and relaxed based on the average chest impedance values. The cardiopulmonary resuscitation device and automated external defibrillator fusion system using chest impedance according to claim 4.

6. The control unit calculates the absolute value of the difference between each chest impedance value measured continuously by the chest impedance measurement unit when the patient's chest is compressed and relaxed and the average value of a certain number of chest impedance values among the chest impedance values when the patient's chest is compressed and relaxed, and detects that a variation has occurred in the chest impedance values when the patient's chest is compressed and relaxed stored in the second storage unit. The cardiopulmonary resuscitation device and automated external defibrillator fusion system using chest impedance according to claim 5.

7. When the absolute value of the difference between the average value of each chest impedance and each chest impedance value when the patient's chest is compressed and relaxed is a value equal to or greater than a predetermined absolute value, the control unit excludes the average chest impedance values before the variation stored in the second storage unit, replaces them with the chest impedance values measured by the chest impedance measurement unit when the patient's chest is compressed and relaxed after the exclusion of the average chest impedance values, and generates a profile of an optimal biphasic electric shock waveform when the patient's chest is compressed and relaxed using the replaced chest impedance values. The cardiopulmonary resuscitation device and automated external defibrillator fusion system using chest impedance according to claim 6.

8. The cardiopulmonary resuscitation device and the automated external defibrillator fusion system using chest impedance according to claim 7, characterized in that it includes a second notification unit that outputs a message including voice and visual representation when the absolute value of the chest impedance difference calculated by the control unit during chest compression and relaxation is a value equal to or greater than a predetermined absolute value.

9. Regarding the profile of the biphasic electric shock waveform, let the current value before the first phase interval be a, the current value between the first phase interval and the second phase interval be b, the current value after the second phase interval be c, the decreased current decrease amount be α while the peak current decreases in the first phase interval, the decreased current decrease amount when the peak current decreases in the second phase interval be β, the duration in the first phase interval be A, the duration in the second phase interval be B, the difference value between the current value immediately before the end of the first phase interval and the current value immediately before the start of the second phase interval be circled number 1, and the absolute value of the peak current in the first phase interval be circled number 2. Then, a = b = c, α = β, A = B, and circled number 1 + α = circled number 2. The cardiopulmonary resuscitation device and the automated external defibrillator fusion system using chest impedance according to claim 1 are characterized by this.

10. The cardiopulmonary resuscitation device and the automated external defibrillator fusion system using chest impedance according to claim 1, characterized in that the support base is slid from the support plate so that the lower end of the piston moves to a position where it compresses the chest compression point of the patient.

11. The cardiopulmonary resuscitation device and the automated external defibrillator fusion system using chest impedance according to claim 1, characterized in that the support plate includes bands provided with a pair of cuffs on the sides to wrap the upper part of the arm including the elbow of the patient and fix the patient's arm while chest compression of the patient is being performed.

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