WO2021090954A1 - Dispositif de détection de signal de battement cardiaque et programme de détection de signal de battement cardiaque - Google Patents

Dispositif de détection de signal de battement cardiaque et programme de détection de signal de battement cardiaque Download PDF

Info

Publication number
WO2021090954A1
WO2021090954A1 PCT/JP2020/041779 JP2020041779W WO2021090954A1 WO 2021090954 A1 WO2021090954 A1 WO 2021090954A1 JP 2020041779 W JP2020041779 W JP 2020041779W WO 2021090954 A1 WO2021090954 A1 WO 2021090954A1
Authority
WO
WIPO (PCT)
Prior art keywords
signal
heartbeat
capacitor
heartbeat signal
biological signal
Prior art date
Application number
PCT/JP2020/041779
Other languages
English (en)
Japanese (ja)
Inventor
佐藤　敦
小林　宏一郎
守生 岩井
尚樹 本間
Original Assignee
株式会社エクォス・リサーチ
国立大学法人岩手大学
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 株式会社エクォス・リサーチ, 国立大学法人岩手大学 filed Critical 株式会社エクォス・リサーチ
Publication of WO2021090954A1 publication Critical patent/WO2021090954A1/fr

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • A61B5/0245—Detecting, measuring or recording pulse rate or heart rate by using sensing means generating electric signals, i.e. ECG signals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R27/00—Arrangements for measuring resistance, reactance, impedance, or electric characteristics derived therefrom
    • G01R27/02—Measuring real or complex resistance, reactance, impedance, or other two-pole characteristics derived therefrom, e.g. time constant
    • G01R27/26—Measuring inductance or capacitance; Measuring quality factor, e.g. by using the resonance method; Measuring loss factor; Measuring dielectric constants ; Measuring impedance or related variables

Definitions

  • the present invention relates to a heartbeat signal detection device and a heartbeat signal detection program, for example, one that detects a heartbeat signal using a capacity.
  • Routine vital measurement is important for grasping the health condition of the human body, and among them, confirmation of pulse waves is extremely effective as a means for detecting signs of illness, especially abnormalities in the circulatory system. .. Therefore, there is a great demand for vital measuring devices that easily measure pulse waves, and various contact-type and non-invasive / non-contact devices have been developed.
  • a resonance circuit is constructed by using a capacitor, a coil, or the like, and a sensing element connected in parallel with the capacitor is brought closer to the vicinity of the heart of the human body. Since the sensing element and the human body portion of the heart region are capacitively coupled, the pulse of the heart can be detected as a change in the resonance frequency.
  • An object of the present invention is to detect a heartbeat signal more accurately.
  • a first capacitor is placed in a heart region outside the body and is capacitively coupled to an organ extending from the outside of the body to the heart region, and is placed in a lung region outside the body.
  • a second capacitor that is capacitively coupled to an organ extending from the outside of the body to the lung region, a first biological signal that is based on a temporal change in the capacitance of the first capacitor that is capacitively coupled, and the above.
  • a biosignal acquisition means for acquiring a second biometric signal based on a temporal change in the capacitance of the second capacitor coupled with capacitance, the acquired first biometric signal, and the first biometric signal.
  • a heartbeat signal detecting device comprising: a heartbeat signal acquisition means for acquiring a heartbeat signal using the difference of the second biological signal synchronized with the above, and an output means for outputting the acquired heartbeat signal.
  • the invention according to claim 2 provides the heartbeat signal detection device according to claim 1, wherein the electrode area of the first capacitor is larger than the electrode area of the second capacitor.
  • the invention according to claim 3 includes the first resonance circuit using the first capacitor and the second resonance circuit using the second capacitor, and obtains the biological signal.
  • the means is characterized in that the first biological signal and the second biological signal are acquired, respectively, by using the change in the resonance state of the first resonance circuit and the second resonance circuit, respectively.
  • the heartbeat signal detection device according to claim 1 or 2 is provided.
  • the first resonance circuit and the second resonance circuit fix the drive frequency and the amplitude of the resonance voltage, respectively, and the biological signal acquisition means is the second resonance circuit.
  • the heartbeat signal detecting device according to claim 3, wherein the heartbeat signal detecting device is provided.
  • the invention according to claim 5 comprises an adjusting means for adjusting a voltage value of at least one of a voltage generated in the first coil and a voltage generated in the second coil, and the heartbeat signal.
  • the acquisition means provides the heartbeat signal detection device according to claim 4, wherein the difference is acquired by using the adjusted voltage value.
  • the adjusting means provides the heartbeat signal detecting device according to claim 5, wherein the adjusting means amplifies the voltage value of the voltage generated in the second coil.
  • the heartbeat signal according to claim 6, wherein the adjusting means performs the amplification by shifting a bit representing a voltage generated in the second coil.
  • a detection device is provided.
  • the first capacitor is placed in the heart region outside the body and is capacitively coupled to the organ extending from the outside of the body to the heart region, and is arranged in the lung region outside the body.
  • a biometric signal acquisition function for acquiring a first biometric signal based on the temporal change of the above and a second biometric signal based on the temporal change of the capacitance of the second capacitor coupled with capacitance, and the above-mentioned A heartbeat signal acquisition function that acquires a heartbeat signal using the difference between the acquired first biometric signal and the second biometric signal that synchronizes with the first biometric signal, and an output function that outputs the acquired heartbeat signal.
  • the heartbeat signal can be detected more accurately by the difference from the respiratory component.
  • the heartbeat signal detection device 11 includes a resonance circuit 1a for detecting a heartbeat and respiration signal due to heartbeat and respiration, and a resonance circuit 1b for detecting a respiration signal due to respiration.
  • the resonance circuit 1a includes a flat plate type capacitor 3a (FIG. 6) to be mounted at the position of the heart of the subject 10, and the resonance circuit 1b includes a flat plate type capacitor 3b to be mounted at the position of the lungs.
  • the capacitor 3a has an electrode formed larger than that of the capacitor 3b, and the inner part of the body is defined as a measurement region (hatched portion in FIGS. 5A and 5B) than the capacitor 3b.
  • the capacitor 3a detects the beat due to the heartbeat and the movement due to the respiration of the lungs around it as a change in capacitance
  • the capacitor 3b detects the movement due to the respiration of the lung as a change in capacitance. To do.
  • the resonance circuit 1a (FIG. 1 (a)) transmits a heartbeat / breathing signal that combines heartbeat and breathing due to the voltage of the coil 5a caused by the change in resonance frequency.
  • the resonant circuit 1b (not shown) detects the breathing signal due to breathing by the voltage of the coil 5b.
  • the signal processing device 16 (FIG. 2) removes the respiratory component contained in the heartbeat / breathing signal by subtracting the breathing signal from the heartbeat / breathing signal, thereby outputting the heartbeat signal which is the difference between the two.
  • the heartbeat signal detection device 11 can be mounted on the vehicle to monitor the physical condition of the driver. In this case, if the capacitors 3a and 3b are built in the driver's seat or seat belt, these can be carried out without burdening the driver. Can be attached.
  • FIG. 1 is a diagram for explaining the operating principle of the resonant circuit 1a according to the present embodiment.
  • the heartbeat signal detection device 11 includes a resonance circuit 1a for detecting a signal (hereinafter referred to as a heartbeat / respiration signal) in which the movement of the subject 10 due to the heartbeat and the movement of the lungs due to the respiration overlap.
  • a resonance circuit 1b for detecting a signal (hereinafter referred to as a respiratory signal) obtained from the movement of the lungs due to respiration is provided, and FIG. 1 shows the configuration of the resonance circuit 1a among these.
  • the components for the heartbeat / respiration signal will be represented by the capacitors 3a and the like, and the components for the respiration signal will be represented by the capacitors 3b and the like and b. It will be expressed without subscripts such as capacitor 3.
  • the resonance circuit 1a is configured by using an RLC series circuit in which a transmitter 6a, a resistor 2a, a capacitor 3a, and a coil 5a are connected in series.
  • the capacitor 3a is a flat plate type capacitor, and is formed by arranging electrodes 31a and 32a on both sides of the dielectric plate 33a.
  • the electrode 34a will be described later with reference to FIG.
  • the electrode 31a is formed on the side facing the body surface of the subject 10, and the electrode 32a is formed on the side facing the body surface.
  • the transmitter 6a is an AC power supply that supplies power to the resonance circuit 1a, one power supply terminal is connected to one terminal of the resistor 2a, the other power supply terminal is grounded, and one terminal of the coil 5a is connected. You are connected.
  • the other terminal of the resistor 2a is connected to the electrode 31a of the capacitor 3a, and the other terminal of the coil 5a is connected to the electrode 32a.
  • the resonance frequency fr of the resonance circuit 1a is 1 divided by the square root of LC and 2 ⁇ as shown in the equation (1). It is represented by a value, and in the present embodiment, the resonance frequency fr is set to be about 100 [KHz].
  • the capacitor 3a of the resonance circuit 1a configured in this way is attached to the chest of the subject 10 and the transmitter 6a is started, the capacitor 3a is driven by an alternating current. Then, the capacitor 3a is capacitively coupled (coupling) with the internal organs (blood flow through the heart, lungs, arteries, etc.) and electrostatically (because the shape of the coupled dielectric changes). The capacity changes according to the movement of these organs. As a result, the resonance frequency of the resonance circuit 1a fluctuates, so that the movement of these organs can be detected by the change in the resonance frequency.
  • the capacitor 3a can be attached while the subject 10 is wearing clothes.
  • the clothing functions as a dielectric material that separates the electrode 31a from the human body.
  • the change in the capacitance of the capacitor 3a can be detected from the change in the resonance frequency as in the prior art of Patent Document 1, but the heartbeat signal detection device 11 detects this by the time change of the voltage Vf generated in the coil 5a. To detect. Since one terminal of the coil 5a is grounded, Vf is also the potential of the other terminal.
  • FIG. 1B shows the frequency characteristics of the resonant circuit 1a.
  • the vertical axis represents the voltage amplitude in [V]
  • the horizontal axis represents the frequency in [Hz].
  • the curve representing the frequency characteristic of the resonance circuit 1a will be referred to as a resonance curve.
  • the resonance curve has a bell shape centered on the resonance frequency, and is constant unless the capacitance of the capacitor 3a changes.
  • the capacitance changes with the cardiopulmonary activity of the heart and lungs. Therefore, at a certain time point, for example, the curve 21 is formed, and at another time point, for example, the curve 22 is formed. It changes from moment to moment.
  • the resonance curve has a bell-shaped shape centered on the resonance frequency at each time, which changes depending on the cardiopulmonary activity, and the change in the resonance frequency (that is, the change in capacitance accompanying the cardiopulmonary activity).
  • the resonance point, width, and height change dynamically accordingly.
  • the heartbeat signal detection device 11 fixes the drive frequency and the amplitude of the output voltage of the transmitter 6a in the vicinity of the resonance frequency of the resonance circuit 1a.
  • so-called fixed point observation with fixed voltage and amplitude is performed in this way, cardiopulmonary activity is observed as a potential difference of resonance amplitude 23.
  • the amplitude becomes the voltage 27 on the curve 21 and the voltage 28 on the curve 22.
  • the potential difference 23 corresponds to a change in the capacitance of the capacitor 3a, that is, a movement of the heart and lungs.
  • the cardiopulmonary activity can be detected as an electric signal by observing the voltage Vf generated in the coil 5a.
  • the resonance circuit 1a is designed to resonate at about 100 [KHz], but the drive frequency is changed in this vicinity, and the frequency at which the heartbeat / respiration signal appears most often is manually or automatically scanned and selected. It can also be configured as follows. The same applies to the resonant circuit 1b.
  • the heartbeat signal detection device 11 measures the voltage of the coil 5a instead of the change in the resonance frequency, it is not necessary to precisely adjust the frequency, and the drive frequency may be in the vicinity of the resonance frequency. This simplifies the configuration of the electric circuit, does not require adjusting the drive frequency for each individual, and is robust (robust) for the measurement of a plurality of subjects 10 having individual differences in physique.
  • the apparatus when detecting the frequency, complicated digital signal processing such as FFT (Fast Fourier Transform) is required, the apparatus becomes large and expensive, and a delay due to the processing time also occurs.
  • FFT Fast Fourier Transform
  • the heartbeat signal detection device 11 measures the change in the voltage of the coil 5a, it does not require calibration for strictly detecting the voltage value, and detects it without delay using a simple analog circuit described later. Processing can be performed.
  • the heart rate signal detection device 11 also detects these by an analog circuit and simple digital processing described later. Can be done.
  • the heartbeat signal detection device 11 is robust against individual differences in the physique of the subject 10, has a simple circuit configuration, and has a low manufacturing cost, and is therefore suitable for mass production and mounting on a vehicle.
  • the resonance circuit 1a has been described above, the configuration of the resonance circuit 1b is also the same.
  • FIG. 2 is a diagram for explaining the configuration of the heartbeat signal detection device 11.
  • the heartbeat signal detection device 11 is a device that detects a heartbeat signal due to a pulse wave, and detects a resonance circuit 1a for detecting a heartbeat / breathing signal, a half-wave rectifying unit 12a, an HPF13a, an LPF14a, an amplifier circuit 15a, and a breathing signal. It is composed of a resonance circuit 1b, a half-wave rectifying unit 12b, an HPF13b, an LPF14b, an amplifier circuit 15b, and a signal processing device 16 that detects a heartbeat signal by differentially processing the heartbeat / breathing signal and the breathing signal.
  • the half-wave rectifier unit 12 half-wave rectifies the output of the resonance circuit 1.
  • HPF13 and LPF14 are a high-pass filter and a low-pass filter, respectively.
  • the amplifier circuit 15a is an amplifier circuit that amplifies a signal.
  • HPF13 and LPF14 are usually used, but in the case of the heartbeat signal detection device 11, it has been found that the measurement can be performed without them. Therefore, in the present embodiment, the normal HPF13 and LPF14 surrounded by the dotted line in FIG. 2 are omitted. As a result, the circuit can be simplified and the cost can be reduced. Further, when the drive frequencies of the transmitter 6a and the transmitter 6b are the same, one transmitter 6 may be shared by the resonance circuit 1a and the resonance circuit 1b.
  • the signal processing device 16 calculates the heartbeat signal by digital processing by calculating the difference between the heartbeat / breathing signal detected by the resonance circuit 1a and the breathing signal detected by the resonance circuit 1b. Since the respiration signal is weaker than the heartbeat respiration signal, the signal processing device 16 amplifies the respiration signal and then performs a subtraction process so that the respiration component is erased from the heartbeat respiration signal. This amplification was performed by multiplying the real number n by n (n was obtained by an experiment), but it can be performed at a higher speed by performing a bit shift operation.
  • the signal level of the respiration signal is adjusted, but the heartbeat respiration signal or both the heartbeat respiration signal and the respiration signal may be adjusted.
  • the respiratory signal may be amplified in an analog manner by the amplifier circuit 15b instead of being digitally processed by the signal processing device 16. Doing this reduces digital processing and allows for faster processing. It is also possible to configure the difference circuit with an analog circuit.
  • the signal may be leveled by integration, but in the case of the signal processing device 16, the respiration signal is simply amplified and subtracted from the heartbeat respiration signal, so the integration is performed. All heartbeat signals including pulsed signals can be output in real time without delay without complicated digital processing including.
  • FIG. 3 is a diagram for explaining a hardware configuration of the signal processing device 16.
  • a CPU Central Processing Unit
  • ROM Read Only Memory
  • RAM Random Access Memory
  • an interface 44 an input device 45, an output device 46, a storage device 47, and the like are connected by a bus line. It is composed of.
  • the CPU 41 operates according to the heartbeat signal detection program stored in the storage device 47, controls the resonance circuits 1 to the amplifier circuit 15, calculates the pulse signal from the detected heartbeat / breathing signal and the breathing signal, and the like.
  • the ROM 42 is a read-only memory, and stores basic programs, parameters, and the like when the signal processing device 16 operates.
  • the RAM 43 is a readable and writable memory, and provides a working memory when the CPU 41 processes a heartbeat / respiration signal and a respiration signal to calculate a heartbeat signal.
  • the interface 44 is an interface for connecting the signal processing device 16 and the amplifier circuits 15a and 15b.
  • the input device 45 includes, for example, an input device such as a touch panel, a keyboard, or a mouse, and is used when operating the signal processing device 16.
  • the output device 46 includes a display, a speaker, and the like, and displays a heartbeat signal and outputs an operation sound.
  • the storage device 47 is configured by using a large-capacity storage medium such as a semiconductor device or a hard disk, and stores an OS (Operating System), a heartbeat signal detection program, detected pulse data, and the like.
  • OS Operating System
  • a heartbeat signal detection program detected pulse data, and the like.
  • FIG. 4 is a diagram for explaining the configuration of the capacitor 3.
  • 4 (a) to 4 (c) are views showing a capacitor 3a, (a) is a surface on the opposite side of the human body side (a surface on the side not facing the human body), and (c) is a surface on the human body side. It represents (the surface on the side facing the human body), and (b) represents the cross section.
  • the capacitor 3a is made of a dielectric plate 33a made of a square glass epoxy resin or bakelite having a side of about 10 [cm] and a thickness of about 1 [mm].
  • An electrode 32a made of a copper thin film is formed on the surface opposite to the human body side, and an electrode 31a and an electrode 34a made of a copper thin film are formed on the surface on the human body side.
  • the electrode 32a has a square shape with a side of about 8 [cm] and is arranged at the center of the dielectric plate 33a.
  • a dielectric plate 33a is exposed on the outside of the periphery of the electrode 32a.
  • the electrode 31a has the same size and shape as the electrode 32a, and is formed at a position corresponding to the electrode 32a.
  • an electrode 34a having a width of about 1 [cm] is formed in an annular shape across an exposed surface of the dielectric plate 33a.
  • the electrode 32a and the electrode 31a are connected to the coil 5a and the resistor 2a, respectively, and the electrode 34a is grounded.
  • the resistor 2a may be connected to the electrode 32a, and the coil 5a may be connected to the electrode 31a.
  • FIGS. 4 (d) to (f) are views showing a capacitor 3b, (d) is a surface on the opposite side of the human body side (a surface on the side not facing the human body), and (f) is a surface on the human body side.
  • (E) represents a cross section.
  • the capacitor 3b is configured by using the same member as the capacitor 3a.
  • the thickness of each member of the capacitor 3b is the same as that of the capacitor 3a, but the area of each member is reduced to 25%, and the length of one side is about 5 [cm].
  • the shape of the capacitor 3 has been described above, it is also possible to form the outer shape into a circular shape or an elliptical shape that matches the heart. Further, it is possible to give a three-dimensional shape such as bending the plate surface. For example, based on the size Q of the heart, the capacitor 3a is formed to have a size equal to or larger than Q, while the capacitor 3b is formed to be smaller than Q.
  • FIG. 5 is a diagram for explaining the difference in the measurement region depending on the size of the electrode area of the capacitor 3. According to the experiment of the inventor of the present application, it was found that the larger the area of the electrode, the deeper the body can be used as the measurement region.
  • FIG. 5A shows a measurement area of the capacitor 3a.
  • the capacitor 3a is set to a size that covers the heart from outside the body, and as shown schematically by diagonal lines, the capacitor 3a extends to the deep part of the body to the heart as a measurement area of the heart and the surrounding lungs. Detect movement.
  • FIG. 5B shows the measurement area of the capacitor 3b. Since the electrode area of the capacitor 3b is smaller than that of the capacitor 3a, the movement of the lungs is detected by setting the shallow part of the body as the measurement area as schematically shown by the diagonal line.
  • FIG. 6 is a diagram showing an example of mounting the capacitor 3.
  • a capacitor 3a was placed at the position of the heart on the front side of the subject 10 from above the clothes, and the position of the lungs shifted from the heart (for example, as shown in FIG. 6).
  • a capacitor 3b was installed at the position of the lung on the right side of the subject 10.
  • FIG. 7 is a diagram for explaining the experimental results.
  • FIG. 7A shows a heartbeat / breathing signal 51 by the condenser 3a.
  • the subject 10 also measured the electrocardiogram with a normal electrocardiogram monitor at the same time for comparison, and the electrocardiogram 50 by this is also shown in the figure.
  • the horizontal axis represents the time axis in seconds, which is common to heartbeat / breathing signals and electrocardiograms.
  • the vertical axis on the left side represents the heartbeat / respiration signal, and the vertical axis on the right side represents the value of the electrocardiogram in [mV] units.
  • FIGS. 7 (b) and 7 (c) The same applies to FIGS. 7 (b) and 7 (c).
  • the R wave is a pulse-shaped wave (for example, R wave 55) that rises sharply in the electrocardiogram, and a name is given to a characteristic portion of the electrocardiographic waveform such as the S wave.
  • the measurement of the interval between adjacent R waves, that is, the RR interval is the most important.
  • FIG. 7B shows the respiration signal 52 due to the capacitor 3b. There are some heartbeat-like parts, but they are less clear than the heartbeat-breathing signal due to the predominance of respiratory components.
  • FIG. 7 (c) shows the heartbeat signal 53 generated by the difference between the heartbeat respiration signal and the respiration signal. As shown in the figure, in the heartbeat signal 53, the peaks 56, 56, ... Of the R waves 55 and 55 are clearly detected, and the RR interval is accurately detected.
  • FIG. 8 is a flowchart for explaining the heartbeat detection process performed by the signal processing device 16. The following processing is performed according to the pulse signal detection program stored in the storage device 47 by the CPU 41. It is assumed that the subject 10 is equipped with capacitors 3a and 3b.
  • the CPU 41 communicates with the resonance circuits 1a and 1b via the interface 44, starts the transmitters 6a and 6b, and drives the resonance circuits 1a and 1b (step 5).
  • the resonance circuit 1a starts the detection of the heartbeat respiration signal
  • the resonance circuit 1b starts the detection of the respiration signal.
  • These signals are analog-processed by the half-wave rectifier unit 12a to the amplifier circuit 15a and the half-wave rectifier unit 12b to the amplifier circuit 15b, respectively, and then input to the signal processing device 16 via the interface 44.
  • the CPU 41 samples the heartbeat / respiration signal and the respiration signal input via the interface 44 at a predetermined sampling rate, converts them into digital data, and stores them in the RAM 43 (steps 10 and 15). At this time, the CPU 41 assigns a detection time to the digitized heartbeat / respiration signal and the respiration signal so that the heartbeat / respiration signal detected at the same time can be associated with the respiration signal in chronological order.
  • the CPU 41 amplifies the respiratory signal stored in the RAM 43, and stores the amplified respiratory signal in the RAM 43 (step 20).
  • the CPU 41 reads the corresponding heartbeat / respiration signal in time series and the respiration signal after amplification from the RAM 43, calculates the difference between them, and stores them in the RAM 43 (step 25). As long as the heartbeat signal can be detected normally, the association of the detection times may be slightly different.
  • the CPU 41 outputs the difference stored in the RAM 43 to the output device 46 as a heartbeat signal (step 30).
  • the CPU 41 returns to step 10 when continuing the measurement (step 35; Y), and ends the process after stopping the resonance circuits 1a and 1b when ending the measurement (step 35; N).
  • FIG. 9 is a diagram for explaining a modification of the capacitor 3a.
  • the capacitor 3a according to this modification has an electrode 35a having the same size as the electrode 32a via a dielectric (space in the case of the figure) on the outside of the electrode 32a, and the electrode 35a is grounded. There is. Other configurations are the same as those of the capacitor 3a of the embodiment.
  • the capacitor 3b also includes an electrode 35b (not shown). With this configuration, the influence of external electromagnetic noise on the capacitor 3 can be reduced.
  • FIG. 10 is a diagram for explaining an example of mounting the heartbeat signal detection device 11 on a vehicle.
  • the capacitor 3b is arranged on the seat belt, and the capacitor 3a is arranged (built-in) on the backrest of the seat.
  • the capacitor 3b is placed near the seatbelt in contact with the chest of the subject 10 when the seatbelt is fastened, and the capacitor 3a is placed at the heart when the subject 10 sits on the seat.
  • the capacitor 3 and the internal organs of the subject 10 are capacitively coupled to each other via the clothes worn by the subject 10, the material of the seatbelt, the member of the backrest, and the like, and the heartbeat / breathing signal Respiratory signals can be detected.
  • the subject 10 can wear the capacitors 3a and 3b without any consciousness simply by sitting down and wearing the seatbelt, and can be worn for a long period of time over the operation period. Can be detected. If the electrodes and dielectric of the capacitor 3 are made of a flexible material such as a conductive resin, it can be mounted more comfortably.
  • FIG. 10B shows an example in which the capacitor 3a is built in the seat belt and the capacitor 3b is built in the backrest of the seat. Since the three-point seat belt just covers the heart area, if the capacitor 3a is miniaturized to a size that fits in the seat belt, the heart region of the subject 10 can be monitored well. Further, it is effective to install the capacitor 3b in the vicinity of the lungs displaced from the heart. Further, in the cases of FIGS. 10A and 10B, if a grounding electrode is attached to the handle so that the user's body is grounded by grasping the handle, electromagnetic noise acting on the human body from the outside is generated. Can be removed, and the detection accuracy of the heartbeat signal is improved.
  • the signal processing device 16 may be mounted on a vehicle or may be mounted on a server device.
  • the heartbeat signal detection device 11 includes a transmission / reception device connected to a communication network such as the Internet instead of the heartbeat signal detection device 11, and is detected by the resonance circuits 1a to the amplifier circuit 15a.
  • the heartbeat / breathing signal and the breathing signal detected by the resonance circuits 1b to the amplifier circuit 15b are transmitted to the server device.
  • the server device calculates the heartbeat signal from the heartbeat signal detection device 11 of the embodiment and the modified example described above.
  • Such a configuration can be used, for example, to provide a monitoring device at a taxi or tour bus business establishment to monitor the health condition of the driver.
  • the server device not only the heartbeat signal but also the respiratory state of the driver can be monitored by the respiratory signal.
  • Heartbeat and respiration are indicators that can easily confirm the health condition, but the driver's abnormality can be detected quickly by the heartbeat signal and respiration signal. Furthermore, it can be expanded to other industries such as railway drivers and aircraft pilots.
  • the pulse of the subject 10 can be measured by attaching a parallel plate type capacitor.
  • the pulse can be measured through clothes, long-term measurement can be performed without imposing a mental or physical burden on the subject 10.
  • the signal that can be detected by a capacitive electrode such as a capacitor is weak, it is possible to amplify and detect a minute change by resonating using a resonance circuit.
  • the heartbeat component can be efficiently acquired by taking the difference between the heartbeat breathing signal in which the breathing component and the heartbeat component are mixed and the breathing signal in which the respiratory component is dominant.
  • (6) By incorporating a capacitor into the seat belt or seat in consideration of the vehicle structure, the sensor arrangement and shape can be optimized.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Physiology (AREA)
  • Veterinary Medicine (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Public Health (AREA)
  • Cardiology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Signal Processing (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
  • Measurement Of Resistance Or Impedance (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention a pour objectif de détecter un signal de battement cardiaque avec plus de précision.　Un dispositif de détection de signal de battement cardiaque (11) est pourvu d'un circuit de résonance (1a) pour détecter un battement cardiaque et un signal de respiration dus à un battement cardiaques et une respiration et un circuit de résonance (1b) destiné à détecter un signal de respiration dû à la respiration. Le circuit de résonance (1a) est pourvu d'un condensateur (3a) de type plaque plate qui est ajusté dans la position du cœur d'un sujet (10) et le circuit de résonance (1b) est pourvu d'un condensateur (3b) de type plaque plate qui est ajusté dans la position des poumons. Un dispositif de traitement de signal (16) élimine la composante de respiration contenue dans le signal de battement cardiaque et de respiration en soustrayant le signal de respiration du signal de battement cardiaque et de respiration et fournit ainsi en sortie un signal de battement cardiaque, qui est la différence entre les deux signaux. Le dispositif de détection de signal de battement cardiaque (11) peut être installé dans un véhicule pour surveiller l'état physique d'un conducteur et, dans ce cas, par l'incorporation des condensateurs 3a et 3b dans le siège du conducteur ou la ceinture de sécurité, les condensateurs 3a et 3b peuvent être ajustés sans peser sur le conducteur.
PCT/JP2020/041779 2019-11-08 2020-11-09 Dispositif de détection de signal de battement cardiaque et programme de détection de signal de battement cardiaque WO2021090954A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2019-203335 2019-11-08
JP2019203335A JP7217470B2 (ja) 2019-11-08 2019-11-08 心拍信号検出装置、及び心拍信号検出プログラム

Publications (1)

Publication Number Publication Date
WO2021090954A1 true WO2021090954A1 (fr) 2021-05-14

Family

ID=75849100

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2020/041779 WO2021090954A1 (fr) 2019-11-08 2020-11-09 Dispositif de détection de signal de battement cardiaque et programme de détection de signal de battement cardiaque

Country Status (2)

Country Link
JP (1) JP7217470B2 (fr)
WO (1) WO2021090954A1 (fr)

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2014210127A (ja) * 2013-04-22 2014-11-13 アルプス電気株式会社 生体情報測定装置
US20170209065A1 (en) * 2016-01-27 2017-07-27 Life Detection Technologies, Inc. Systems and Methods for Detecting Physical Changes without Physical Contact

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP6562338B2 (ja) 2015-01-27 2019-08-21 学校法人立命館 静電容量測定システム、及び、センサユニット
JP6901753B2 (ja) 2017-04-28 2021-07-14 学校法人立命館 測定システム及び測定方法

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2014210127A (ja) * 2013-04-22 2014-11-13 アルプス電気株式会社 生体情報測定装置
US20170209065A1 (en) * 2016-01-27 2017-07-27 Life Detection Technologies, Inc. Systems and Methods for Detecting Physical Changes without Physical Contact

Also Published As

Publication number Publication date
JP7217470B2 (ja) 2023-02-03
JP2021074271A (ja) 2021-05-20

Similar Documents

Publication Publication Date Title
EP2827766B1 (fr) Système et procédé pour faciliter une détection réflectométrique d'une activité physiologique
EP2533692B1 (fr) Procédé et appareil destinés à déterminer un signal de respiration
EP3381364B1 (fr) Procédé et dispositif d'évaluation respiratoire
EP2338413B1 (fr) Moniteurs à impulsions cardiaques
US8860504B2 (en) Method and apparatus for measuring biological signal
WO1994017728A1 (fr) Dispositif de contrôle de pression sanguine
WO2012038877A1 (fr) Procédé et appareil servant à surveiller l'activité respiratoire d'un sujet
JP2011024902A (ja) 車両用心電計測装置
US11172844B2 (en) Apparatus and method for detection of dysfunctional breathing
JP2017533034A (ja) アクティグラフィ方法及び装置
WO2020045400A1 (fr) Dispositif de mesure de tension artérielle, dispositif véhicule et programme de mesure de tension artérielle
Goverdovsky et al. Co-located multimodal sensing: A next generation solution for wearable health
Vetter et al. Integration of an electromagnetic coupled sensor into a driver seat for vital sign monitoring: Initial insight
JP2000102515A (ja) 身体状態検出具
CA3120321A1 (fr) Electrode sans contact de detection d'activite electrique physiologique
WO2015178439A2 (fr) Dispositif et méthode d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, et support lisible par un ordinateur comportant un programme d'aide au diagnostic de l'apnée centrale/obstructive du sommeil
WO2021090954A1 (fr) Dispositif de détection de signal de battement cardiaque et programme de détection de signal de battement cardiaque
WO2021090955A1 (fr) Dispositif de détection de signal biologique, serveur de détection de signal de fréquence cardiaque, véhicule, programme de détection de signal biologique et programme de détection de signal de fréquence cardiaque
Mohammadi-Koushki et al. A wearable device for continuous cardiorespiratory System Monitoring
JP6901753B2 (ja) 測定システム及び測定方法
Tadi et al. Automatic identification of signal quality for heart beat detection in cardiac MEMS signals
JP7332723B2 (ja) 心電図（ｅｃｇ）信号のｑｒｓ複合波を検出するためのシステム
WO2020090763A1 (fr) Dispositif de traitement, système, procédé de traitement, et programme
KR101974905B1 (ko) 무구속적 생체신호 측정센서 및 이를 포함하는 생체신호 측정시스템
Erdoğan et al. Microwave noncontact vital sign measurements for medical applications

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 20884499

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 20884499

Country of ref document: EP

Kind code of ref document: A1