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WO2017013995A1 - Dispositif de détection de signal biologique - Google Patents

Dispositif de détection de signal biologique Download PDF

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Publication number
WO2017013995A1
WO2017013995A1 PCT/JP2016/068791 JP2016068791W WO2017013995A1 WO 2017013995 A1 WO2017013995 A1 WO 2017013995A1 JP 2016068791 W JP2016068791 W JP 2016068791W WO 2017013995 A1 WO2017013995 A1 WO 2017013995A1
Authority
WO
WIPO (PCT)
Prior art keywords
support member
attached
pulse wave
biological signal
main body
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/JP2016/068791
Other languages
English (en)
Japanese (ja)
Inventor
亨 志牟田
晋介 中村
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Onkyo Corp
Murata Manufacturing Co Ltd
Original Assignee
Onkyo Corp
Murata Manufacturing Co Ltd
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 Onkyo Corp, Murata Manufacturing Co Ltd filed Critical Onkyo Corp
Priority to JP2017529516A priority Critical patent/JP6379297B2/ja
Publication of WO2017013995A1 publication Critical patent/WO2017013995A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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 for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/024—Measuring pulse rate or heart rate
    • A61B5/0245—Measuring 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
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/251—Means for maintaining electrode contact with the body
    • A61B5/256—Wearable electrodes, e.g. having straps or bands
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
    • A61B5/27—Conductive fabrics or textiles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/296—Bioelectric electrodes therefor specially adapted for particular uses for electromyography [EMG]

Definitions

  • the present invention relates to a biological signal detection apparatus that detects a biological signal.
  • electrodes using a conductive gel are known as biological electrodes used for detection devices that detect biological signals such as electrocardiogram, myoelectricity, and electroencephalogram (see, for example, Patent Documents 1 and 2). ).
  • Patent Document 1 discloses a biomedical electrode-coated pad that is excellent in shape retention, has a moderate moisture release, is electrically stable, and is easy to handle. More specifically, the biomedical electrode-coated pad includes a hydrophilic gel (conductive gel) that can reduce electrical resistance to a living body, and a pad body that fixes the hydrophilic gel.
  • This pad main body has a gel support part that constitutes a plurality of shape retaining frames that are positioned facing the biomedical electrodes and fix the hydrophilic gel, and the hydrophilic gel is retained through the through holes in the shape retaining frame. It is comprised so that it may spread on the front and back both surfaces of a form frame, and may be hold
  • Patent Document 2 when a conductive gel is used on the surface of an electrode, the application of the conductive gel to each electrode is facilitated, and the operation of wiping the conductive gel from the electrode surface and the living body is facilitated.
  • An electrode pad that can be seen is disclosed. More specifically, this electrode pad is configured such that the convex region of the base member engages with the groove concave portion of the abdominal electrode. Thereby, the pad for abdominal electrodes is fixed to the abdominal electrode. At that time, the lower surface side of the conductive gel provided on the abdominal electrode pad comes into contact with the upper surface portion of the abdominal electrode so as to be electrically conductive.
  • the conductive gel is fixed to the shape retaining frame through the through hole of the shape retaining frame.
  • the strength of the conductive gel is weak, it is necessary to increase the thickness of the conductive gel.
  • the gel electrode is formed on both the front and back surfaces of the shape retaining frame, so that the total thickness is increased.
  • the electrode pad disclosed in Patent Document 2 described above has a structure in which the end of the conductive gel is entirely covered with a shape retaining frame. It is said. As a result, because of the frame, it is difficult to arrange a plurality of (other) bioelectrodes and sensors at high density. In addition, the biomedical electrode coating pad of Patent Document 1 described above has the same problem.
  • the present invention has been made to solve the above-described problems, and an object of the present invention is to provide a biological signal detection device capable of arranging biological electrodes, sensors, and the like with higher density.
  • a biological signal detection apparatus includes a flexible conductor for detecting a biological signal, a substantially thin plate-like support member to which the conductor is attached, and a main body portion to which the support member is attached.
  • the support member is configured to be detachable from the main body, and the main body has an input terminal that is connected in contact with a conductor attached to the support member when the support member is mounted.
  • the flexible conductor is attached from the front surface to the back surface of the substantially thin plate-like support member, and the support member is attached to the main body.
  • the support member is configured to be detachable from the main body, and when the support member is attached, the main body is in contact with and connected to the conductor attached to the support member. It has a terminal. Since the conductor is fixed to the support member and a frame for fixing is unnecessary, other biological electrodes, sensors, and the like can be disposed in the vicinity. As a result, it is possible to arrange bioelectrodes, sensors, and the like with higher density.
  • the conductor since the flexible conductor is used, the conductor can be stably adhered to the living body. Similarly, contact (electrical connection) between the flexible conductor and the input terminal can be stabilized. Furthermore, when the conductor is soiled or torn, it can be easily replaced.
  • the conductor is formed in a substantially cylindrical shape and attached to a support member.
  • the conductor is formed in a substantially cylindrical shape, the conductor can be easily attached by covering the support member.
  • the conductor is formed in a flat shape and is wound around and attached to a support member.
  • the conductor since the conductor is formed in a planar shape, it can be easily attached by winding the conductor around the support member. Note that a conductor (planar shape) that is easier to manufacture can be used as the conductor.
  • the conductor is preferably made of a conductive cloth or a conductive film.
  • the conductor is made of a conductive cloth or a conductive film, the thickness of the bioelectrode can be reduced.
  • a material that can be used as an input terminal in contact with a conductor is not limited without oxidizing a metal like a conductive gel.
  • the skin does not swell due to contact with the skin for a long time.
  • a conductive cloth is used for the conductor, for example, it is possible to prevent discomfort caused by contact with a cooled conductor (conductive gel, metal, etc.) when worn in winter or the like.
  • the biological signal detection device further includes a pulse wave sensor that is disposed in the vicinity of the support member attached to the main body portion and detects a pulse wave signal, and the conductor detects an electrocardiogram signal.
  • a pulse wave sensor that is disposed in the vicinity of the support member attached to the main body portion and detects a pulse wave signal, and the conductor detects an electrocardiogram signal.
  • An electrocardiographic electrode is preferable.
  • the pulse wave sensor for detecting the pulse wave signal is disposed in the vicinity of the support member, it is possible to simultaneously acquire the pulse wave signal in addition to the electrocardiographic signal. Therefore, for example, biological information such as pulse wave propagation time can be measured.
  • the biological signal detection apparatus preferably includes a neckband to which the main body is attached and which can be worn along the circumferential direction of the user's neck.
  • the main body is attached and a neckband that can be worn along the circumferential direction of the user's neck is provided, making it easy to fit the user's neck and making stable contact with the neck. Can do.
  • the biological signal detection apparatus preferably includes a breast band to which the main body portion is attached and which can be worn on the chest of the user.
  • the main body portion is attached and the chest band that can be worn on the user's chest is provided, it is easy to fit the user's chest and can be stably brought into contact with the chest.
  • FIG. 1 is a diagram illustrating a state in which the biological signal detection device 1 is mounted on a user's neck.
  • FIG. 2 is a perspective view illustrating a configuration of the sensing unit 11 included in the biological signal detection device 1.
  • FIG. 3 is a block diagram showing a functional configuration of the biological signal detection apparatus 1.
  • the biological signal detection device 1 includes a substantially U-shaped (or substantially C-shaped) neckband 13 that is elastically mounted so as to sandwich the neck from the back side of the user's neck, and is disposed at both ends of the neckband 13. It is provided with a pair of sensing units 11 and 12 that come in contact with both sides of the user's neck.
  • the neckband 13 can be worn along the circumferential direction of the user's neck. That is, as shown in FIG. 1, the neckband 13 is worn along the back of the user's neck from one side of the user's neck to the other side of the neck. More specifically, the neck band 13 includes, for example, a belt-shaped plate spring and a rubber tube that covers the plate spring. Therefore, the neckband 13 is urged so as to shrink inward, and when the user wears the neckband 13, the neckband 13 (sensing units 11 and 12) is in contact with the neck of the user. Retained.
  • a rubber tube it is preferable to use what has biocompatibility as a rubber tube. Moreover, it can replace with a rubber tube and can use the tube which consists of plastics, for example.
  • a cable for electrically connecting both sensing units 11 and 12 is also wired. Here, it is desirable that the cable be coaxial in order to reduce noise.
  • the sensing unit 11 (12) is mainly flexible and has a conductive cloth 15 (corresponding to the conductor described in the claims) that detects a biological signal (for example, an electrocardiogram signal). ), A substantially thin plate-like electrode support member 112 to which the conductive cloth 15 is attached (corresponding to the support member described in the claims), and a main body 111 to which the electrode support member 112 is detachably attached. Yes.
  • one sensing unit 11 has a photoelectric pulse wave sensor 20 in addition to the above configuration.
  • the conductive cloth 15 is used as an electrode for detecting an electrocardiogram signal.
  • the electrocardiogram signal for example, a myoelectric signal or a sweating amount may be detected.
  • a piezoelectric pulse wave sensor instead of or in addition to the photoelectric pulse wave sensor 20, a piezoelectric pulse wave sensor, an oxygen saturation sensor, a sound sensor (microphone), a displacement sensor, an acceleration sensor, a temperature sensor, a humidity sensor, or the like may be used.
  • the conductive cloth 15 serving as an electrocardiographic electrode (hereinafter, the conductive cloth 15 may be referred to as the electrocardiographic electrode 15), a woven fabric or a knitted fabric made of conductive yarn having conductivity is used.
  • the conductive cloth 15 is formed in a substantially cylindrical shape and is attached to the electrode support member 112.
  • the conductive yarn for example, a resin yarn whose surface is plated with Ag, a carbon nanotube-coated one, or a conductive polymer such as PEDOT may be used.
  • PEDOT a conductive polymer which has electroconductivity.
  • the conductive cloth 15 is preferably subjected to end treatment such as folding four sides and sewing with a sewing machine, or cutting and welding treatment using laser or ultrasonic waves.
  • end treatment such as folding four sides and sewing with a sewing machine, or cutting and welding treatment using laser or ultrasonic waves.
  • the conductive cloth 15 formed in a substantially cylindrical shape may be formed in a substantially cylindrical shape by rounding a planar conductive cloth and stitching together corresponding two sides or overlapping a part thereof.
  • the conductive cloth 15 can be mounted on the electrode support member 112.
  • the conductive cloth 15 ⁇ / b> B may be formed in a strip shape (planar shape) and wound around the electrode support member 112 for attachment. At that time, the conductive cloth 15B wound around the electrode support member 112 is preferably fixed with, for example, a double-sided tape or an adhesive.
  • a conductive film having flexibility may be used instead of the conductive cloth 15.
  • the electrode support member 112 to which the conductive cloth 15 is attached is formed in a substantially thin plate shape, for example, with resin.
  • the electrode support member 112 includes a flat portion to which the conductive cloth 15 is attached, and curved portions formed on both sides of the flat portion so as to be continuous with the flat portion.
  • a claw portion (engagement claw) 112a that engages with a groove portion 111a of the main body 111, which will be described later, is formed at the end of each curved portion.
  • the electrode support member 112 can be attached to and detached from the main body 111 by the claw portion (engagement claw) 112a. Since the conductive cloth 15 is stretchable, as shown in FIG. 2, the conductive cloth 15 can be easily set (or spread) by covering the electrode support member 112 with the opening of the substantially cylindrical conductive cloth 15 wide. Exchange). At the same time, the conductive cloth 15 and an input terminal 14 described later are electrically connected.
  • the main body 111 is made of, for example, a resin so that it has a thin, substantially bowl shape, that is, when viewed in a cross-section along the short side, the surface in contact with the neck draws an arc. Thereby, a feeling of wearing is improved.
  • the electrode support member 112 is detachably attached to the main body 111.
  • the main body 111 is formed such that the region where the electrode support member 112 fits is recessed by the thickness of the electrode support member 112 (or deeper than the thickness). Further, a groove (engagement groove) 111a is formed on the side surface of the region of the main body 111 where the electrode support member 112 is fitted. Then, the electrode support member 112 is fixed (locked) to the main body portion 111 by fitting the claw portions 112a formed at both ends of the electrode support member 112 into the groove portion 111a. That is, as shown in FIG. 2, the conductive cloth 15 can be easily set (or replaced) by mounting (locking) the electrode support member 112 to which the conductive cloth 15 is attached to the main body 111. The electrode support member 112 may be fixed to the main body 111 by a method such as screwing.
  • the input terminal 14 is disposed at a position facing the back surface of the electrode support member 112 (conductive cloth 15) of the main body 111. By attaching the electrode support member 112 to the main body 111, the back surface of the conductive cloth 15 attached to the electrode support member 112 and the input terminal 14 come into contact with each other and are electrically connected.
  • the conductive cloth 15 is connected to a signal processing unit 31 described later via the input terminal 14.
  • a photoelectric pulse wave that has a light emitting element 201 and a light receiving element 202 in the vicinity of the electrode support member 112 (conductive cloth 15) on the surface of the main body 111 (the surface that contacts the neck), and detects a photoelectric pulse wave signal.
  • a sensor 20 is provided.
  • the photoelectric pulse wave sensor 20 is a sensor that optically detects a photoelectric pulse wave signal using the light absorption characteristic of blood hemoglobin.
  • the light emitting element 201 emits light according to a pulsed drive signal output from a drive unit 350 of the signal processing unit 31 described later.
  • a drive unit 350 of the signal processing unit 31 for example, an LED, a VCSEL (Vertical Cavity Surface Emitting LASER), or a resonator type LED can be used.
  • the driving unit 350 generates and outputs a pulsed driving signal for driving the light emitting element 201.
  • the light receiving element 202 outputs a detection signal corresponding to the intensity of light irradiated from the light emitting element 201 and transmitted through the neck or reflected from the neck.
  • a photodiode or a phototransistor is preferably used as the light receiving element 202.
  • a photodiode is used as the light receiving element 202.
  • the light receiving element 202 is connected to the signal processing unit 31, and a detection signal (photoelectric pulse wave signal) obtained by the light receiving element 202 is output to the signal processing unit 31.
  • a battery (not shown) that supplies electric power to the photoelectric pulse wave sensor 20, the signal processing unit 31, the wireless communication module 60, and the like is accommodated in one sensing unit 11 (main body unit 111).
  • a signal processing unit 31 and wireless communication for transmitting biological information such as a measured electrocardiogram signal, photoelectric pulse wave signal, and pulse wave propagation time to an external device.
  • the module 60 is accommodated.
  • the sensing units 11 and 12 (conductive cloths 15 and 15) and the photoelectric pulse wave sensor 20 are each connected to a signal processing unit 31, and the detected electrocardiogram signal and photoelectric pulse wave signal are sent to the signal processing unit 31. Entered.
  • the signal processing unit 31 measures the pulse wave propagation time from the time difference between the R wave peak of the detected electrocardiogram signal (cardiac radio wave) and the peak of the first photoelectric pulse wave signal (pulse wave).
  • the signal processing unit 31 processes the input electrocardiogram signal and measures a heart rate, a heart beat interval, and the like. Further, the signal processing unit 31 processes the input photoelectric pulse wave signal to measure the pulse rate, the pulse interval, and the like.
  • the signal processing unit 31 includes amplification units 311 and 321, a first signal processing unit 310, a second signal processing unit 320, peak detection units 316 and 326, peak correction units 318 and 328, and a pulse wave propagation time measurement unit 330. is doing.
  • the first signal processing unit 310 includes an analog filter 312, an A / D converter 313, and a digital filter 314.
  • the second signal processing unit 320 includes an analog filter 322, an A / D converter 323, a digital filter 324, and a second-order differentiation processing unit 325.
  • the digital filter 314, 324, the second-order differentiation processing unit 325, the peak detection units 316, 326, the peak correction units 318, 328, and the pulse wave propagation time measurement unit 330 are CPUs that perform arithmetic processing.
  • a ROM for storing a program and data for causing the CPU to execute each process, a RAM for temporarily storing various data such as calculation results, and the like are included. That is, the functions of the above-described units are realized by executing the program stored in the ROM by the CPU.
  • the amplifying unit 311 is configured by an amplifier using, for example, an operational amplifier, and amplifies the electrocardiogram signals detected by the sensing units 11 and 12 (conductive cloths 15 and 15).
  • the electrocardiographic signal amplified by the amplifying unit 311 is output to the first signal processing unit 310.
  • the amplification unit 321 is configured by an amplifier using an operational amplifier, for example, and amplifies the photoelectric pulse wave signal detected by the photoelectric pulse wave sensor 20.
  • the photoelectric pulse wave signal amplified by the amplification unit 321 is output to the second signal processing unit 320.
  • the first signal processing unit 310 includes the analog filter 312, the A / D converter 313, and the digital filter 314, and performs filtering processing on the electrocardiogram signal amplified by the amplification unit 311. This extracts the pulsation component.
  • the second signal processing unit 320 includes the analog filter 322, the A / D converter 323, the digital filter 324, and the second-order differentiation processing unit 325, and the photoelectric pulse amplified by the amplification unit 321.
  • a pulsating component is extracted by applying filtering processing and second-order differentiation processing to the wave signal.
  • Analog filters 312, 322 and digital filters 314, 324 remove components (noise) other than the frequency characterizing the electrocardiogram signal and photoelectric pulse wave signal, and perform filtering to improve S / N. More specifically, a frequency component of 0.1 to 200 Hz is generally dominant for an electrocardiogram signal, and a frequency component of 0.1 to several tens of Hz is dominant for a photoelectric pulse wave signal.
  • the S / N is improved by performing filtering using the analog filters 312 and 322 and the digital filters 314 and 324 and selectively passing only signals in the frequency range.
  • the purpose is to extract only the pulsating component (that is, when it is not necessary to acquire a waveform or the like), a component other than the pulsating component by narrowing the pass frequency range to improve noise resistance. May be blocked.
  • the analog filters 312, 322 and the digital filters 314, 324 are not necessarily provided, and only one of the analog filters 312, 322 and the digital filters 314, 324 may be provided. Note that the electrocardiogram signal subjected to the filtering process by the analog filter 312 and the digital filter 314 is output to the peak detection unit 316. Similarly, the photoelectric pulse wave signal subjected to the filtering process by the analog filter 322 and the digital filter 324 is output to the second-order differentiation processing unit 325.
  • the second-order differentiation processing unit 325 obtains a second-order differential pulse wave (acceleration pulse wave) signal by second-order differentiation of the photoelectric pulse wave signal.
  • the acquired acceleration pulse wave signal is output to the peak detector 326.
  • the peak (rising point) of the photoelectric pulse wave is not clearly changed and may be difficult to detect. Therefore, it is preferable to detect the peak by converting it to an acceleration pulse wave.
  • a second-order differential processing unit 325 is provided. Is not essential and may be omitted.
  • the peak detection unit 316 detects the peak (R wave) of the electrocardiogram signal that has been subjected to signal processing by the first signal processing unit 310 (the pulsating component has been extracted).
  • the peak detection unit 326 detects the peak of the photoelectric pulse wave signal (acceleration pulse wave) subjected to the filtering process by the second signal processing unit 320.
  • Each of the peak detection unit 316 and the peak detection unit 326 performs peak detection within the normal range of the heartbeat interval and the pulse interval, and information on the peak time, peak amplitude, and the like for all detected peaks is stored in the RAM or the like. save.
  • the peak correction unit 318 obtains the delay time of the electrocardiogram signal in the first signal processing unit 310 (analog filter 312 and digital filter 314). The peak correction unit 318 corrects the peak of the electrocardiogram signal detected by the peak detection unit 316 based on the obtained delay time of the electrocardiogram signal. Similarly, the peak correction unit 328 obtains the delay time of the photoelectric pulse wave signal in the second signal processing unit 320 (analog filter 322, digital filter 324, second-order differentiation processing unit 325). The peak correction unit 328 corrects the peak of the photoelectric pulse wave signal (acceleration pulse wave signal) detected by the peak detection unit 326 based on the obtained delay time of the photoelectric pulse wave signal. The corrected peak of the electrocardiogram signal and the corrected peak of the photoelectric pulse wave signal (acceleration pulse wave) are output to the pulse wave propagation time measurement unit 330. Note that providing the peak correction unit 318 is not essential and may be omitted.
  • the pulse wave propagation time measurement unit 330 is configured to detect an interval (time difference) between the R wave peak of the electrocardiogram signal corrected by the peak correction unit 318 and the peak of the photoelectric pulse wave signal (acceleration pulse wave) corrected by the peak correction unit 328. ) To determine the pulse wave propagation time.
  • the pulse wave propagation time measurement unit 330 calculates, for example, a heart rate, a heartbeat interval, a heartbeat interval change rate, and the like from an electrocardiogram signal in addition to the pulse wave propagation time. Similarly, the pulse wave propagation time measurement unit 330 calculates a pulse rate, a pulse interval, a pulse interval change rate, and the like from the photoelectric pulse wave signal (acceleration pulse wave).
  • the acquired measurement data such as pulse wave propagation time, heart rate, and pulse rate is transmitted to, for example, a PC, a portable music player having a display, a smartphone, or the like via the wireless communication module 60.
  • the electrocardiogram signal and the photoelectric pulse wave signal are detected using the electrocardiogram signal measuring apparatus 1 and the pulse wave propagation time is measured, as shown in FIG. And the sensing units 11 and 12 (the conductive cloths 15 and 15 and the photoelectric pulse wave sensor 20) are brought into contact with the neck.
  • an electrocardiogram signal between the two sensing units 11 and 12 is detected, and at the same time, a photoelectric pulse wave signal is detected by the photoelectric pulse wave sensor 20. Then, the pulse wave propagation time is acquired from the peak time difference between the electrocardiogram signal and the photoelectric pulse wave signal. Since the method for acquiring the pulse wave propagation time is as described above, detailed description thereof is omitted here.
  • the user can detect and measure an electrocardiogram signal, a photoelectric pulse wave signal, a pulse wave propagation time, and the like only by wearing the biological signal detection device 1 on the neck.
  • biological information such as the detected and measured electrocardiogram signal, photoelectric pulse wave signal, and pulse wave propagation time is transmitted to an external device by the wireless communication module 60.
  • the flexible conductive cloth (electrocardiographic electrode) 15 is attached from the front surface to the back surface of the substantially thin plate-like electrode support member 112, and the electrode A support member 112 is attached to the main body 111.
  • the electrode support member 112 is configured to be detachable from the main body 111, and the main body 111 is electrically conductive on the back side of the electrode support member 112 when the electrode support member 112 is attached.
  • the input terminal 14 is connected in contact with 15. Since the conductive cloth 15 is fixed to the support member 112 and does not require a frame for fixing, the other conductive electrodes and sensors (for example, the photoelectric pulse wave sensor 20) can be disposed in the vicinity. .
  • the biological signal detection apparatus 1 since the flexible conductive cloth 15 is used, the conductive cloth 15 can be stably adhered to the living body (skin). Similarly, contact (electrical connection) between the conductive cloth 15 having flexibility and the input terminal 14 can be stabilized. Furthermore, when the conductive cloth 15 is dirty or torn, it can be easily replaced.
  • the conductive cloth 15 is formed in a substantially cylindrical shape, the conductive cloth 15 can be easily attached by covering the electrode supporting member 112.
  • the conductive cloth 15B when the conductive cloth 15B is formed in a strip shape (planar shape), the conductive cloth 15B can be easily attached by winding the conductive cloth 15B around the electrode support member 112. As the electrocardiographic electrode, a strip (planar) that is easier to produce can be used.
  • a conductive cloth or a conductive film is used as the electrocardiographic electrode 15, the thickness of the electrocardiographic electrode 15 can be reduced.
  • a material that can be used as the input terminal 14 that is in contact with the electrocardiogram electrode 15 does not oxidize a metal unlike a conductive gel, and is not limited.
  • the skin does not swell due to contact with the skin for a long time.
  • a conductive cloth is used for the electrocardiogram electrode 15, for example, when a conductive gel or metal is used, the discomfort caused by touching the cooled electrocardiogram electrode when worn in winter or the like is prevented. You can also
  • the photoelectric pulse wave sensor 20 is disposed in the vicinity of the electrode support member 112, it is possible to simultaneously acquire a photoelectric pulse wave signal in addition to the electrocardiographic signal. Therefore, for example, biological information such as pulse wave propagation time can be measured.
  • the main body 111 is attached and the neckband 13 that can be worn along the circumferential direction of the user's neck is provided, the user can easily fit the user's neck, It can be contacted stably.
  • the neck is a part that is relatively easy to sweat, even if the conductive cloth 15 is soiled by attaching the biological signal detection device 1 to the neck for a long time, the electrode support member 112 is replaced. It can be easily replaced with a new conductive cloth 15.
  • the pair of sensing units 11 and 12 are configured to have a neckband configuration in which both ends of the neckband 13 are attached. It can also be set as the structure of the chest band type (chest strap type) attached to the chest band (chest strap) to wear.
  • FIG. 5 is a diagram illustrating a state in which the biological signal detection device 2 is mounted on the chest of the user.
  • FIG. 6 is a front view and a cross-sectional view showing the configuration of the biological signal detection device 2.
  • the biological signal detection apparatus 2 includes a chest band (chest strap) 26 that can be attached to the chest of a user, a single body portion 211 attached to the chest band 26, and a body portion that is arranged in the longitudinal direction of the chest band 26.
  • Two (or two or more) electrode support members 212 (conductive cloth 25) detachably attached to 211 are provided.
  • Two input terminals 24 are installed in the main body 211.
  • the pair of electrode support members 212 and 212 to which the conductive cloth 25 is attached are attached to the main body 211, so that the conductive cloth 25 and the input terminal 24 are electrically connected.
  • the chest band (chest strap) 26 is integrated with the main body 211, and a through-hole penetrating the chest band 26 in the thickness direction is formed at the position of the input terminal 24. Therefore, when the electrode support member 212 is attached, the conductive cloth 25 and the input terminal 24 come into contact (that is, are electrically connected) through the through hole.
  • Other configurations are the same as or similar to those of the biological signal detection apparatus 1 described above, and thus detailed description thereof is omitted here.
  • the main body 211 is integrated with the chest band (chest strap) 26, but the main body 211 is separated from the chest band (chest strap) 26, and It is good also as a structure fixed to the chest band 26 by the electrode support members 212,212.
  • other sensors than the electrocardiographic electrode 25 are not shown, but other sensors (for example, a photoelectric pulse wave sensor) are arranged in the vicinity of the electrocardiographic electrode (conductive cloth) 25. It is also preferable to do.
  • the electrocardiogram signal measuring apparatus 2 When an electrocardiogram signal or the like is measured using the electrocardiogram signal measuring apparatus 2, the electrocardiogram signal measuring apparatus 2 (sensing unit 21) is connected to the chest by a chest band (chest strap) 26 as shown in FIG. The sensing unit 21 (two conductive cloths 25, 25) is brought into contact with the chest. By doing so, an electrocardiogram signal is detected by the sensing unit 21 (two conductive cloths 25, 25).
  • the user can detect and measure the electrocardiogram signal simply by wearing the biological signal detection device 2 on the chest.
  • the biometric information such as the detected / measured electrocardiographic signal is transmitted to an external device by the wireless communication module 60.
  • FIG. 7 shows a biological signal detection device 2B according to a first modification of the second embodiment.
  • FIG. 7 is a front view and a cross-sectional view showing the configuration of the biological signal detection device 2B according to the first modification of the second embodiment.
  • the biological signal detection device 2 ⁇ / b> B has a pair (two) of conductive cloths (hearts) instead of the pair (two) of electrode support members 212 and 212 each having a conductive cloth 25 attached thereto.
  • This is different from the biological signal detection device 2 described above in that it has a single electrode support member 212B (integrated electrode support member 212B) to which the electric electrodes) 25, 25 are attached. That is, in the biological signal detection device 2B, one (integrated) electrode support member 212B is detachably attached to one main body portion 211B, and two (a pair) of conductive cloths (cores) are attached to the electrode support member 212B.
  • (Electrical electrodes) 25 and 25 are different from the biological signal detection device 2 described above in that they are attached. Other configurations are the same as or similar to those of the biological signal detection apparatus 2 described above, and thus detailed description thereof is omitted here.
  • FIG. 8 shows a biological signal detection device 2C according to a second modification of the second embodiment.
  • FIG. 8 is a front view and a longitudinal sectional view showing a configuration of a biological signal detection device 2C according to a second modification of the second embodiment.
  • the biological signal detection device 2C includes an electrode support member 212C and a pair of conductive cloths (bioelectrodes) 25 and 25 attached to the electrode support member 212C of a chest band (chest strap) 26C. It is different from the above-described biological signal detection device 2B in that it is arranged along the short direction. That is, in the biological signal detection device 2 ⁇ / b> C, a pair of conductive cloths (electrocardiographic electrodes) 25 and 25 are arranged in a direction substantially perpendicular to the longitudinal direction of the chest band 26. Other configurations are the same as or similar to those of the biological signal detection device 2B described above, and thus detailed description thereof is omitted here.
  • the user since the main body portions 211, 211B, and 211C are attached and the chest bands (chest straps) 26, 26B, and 26C that can be attached to the chest of the user are provided, the user It can be easily fitted to the chest and can be stably brought into contact with the chest.
  • the chest is a relatively sweaty part, the electrode support members 212, 212 ⁇ / b> B, and 212 ⁇ / b> C are replaced even if the conductive cloth 25 becomes dirty by attaching the biological signal detection device 2 to the chest for a long time.
  • the new conductive cloth 25 can be easily replaced.
  • the biological signal detection apparatus 1 includes the photoelectric pulse wave sensor 20, but may be configured not to include the photoelectric pulse wave sensor 20.
  • the pair of sensing units 11 and 12 are attached to both ends of the neckband 13, but the sensing units 11 and 12 are not necessarily attached to both ends of the neckband 13. Further, the neckband 13 may be configured such that its length can be adjusted by an adjusting mechanism or the like.
  • the wireless communication module 60 transmits biological information (measurement data) such as an electrocardiogram signal, a photoelectric pulse wave signal, and a pulse wave propagation time detected and measured to an external device.
  • biological information such as an electrocardiogram signal, a photoelectric pulse wave signal, and a pulse wave propagation time detected and measured to an external device.
  • the acquired biological information may be stored in a memory in the apparatus, and the data may be transferred by connecting to an external device after the measurement is completed.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Surgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Biophysics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Physics & Mathematics (AREA)
  • Animal Behavior & Ethology (AREA)
  • Pathology (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Cardiology (AREA)
  • Signal Processing (AREA)
  • Physiology (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

L'invention concerne un dispositif de détection de signal biologique (1) qui est pourvu : d'une bande entourant le cou (13) pouvant être montée de manière circonférentielle autour du cou d'un utilisateur; et d'une paire d'unités de détection (11, 12) qui sont fixées sur les deux extrémités de la bande entourant le cou (13) et détectent un signal biologique. Les unités de détection (11 (12)) sont pourvues : d'un tissu conducteur (15) souple (électrocardioélectrode) pour détecter un signal électrocardiographique; d'un élément support d'électrode (112), sensiblement en forme de plaque mince, auquel le tissu conducteur (15) est fixé; et d'un corps principal (111) sur lequel l'élément support d'électrode (112) est monté. L'élément support d'électrode (112) est configuré pour pouvoir être fixé au corps principal (111) et détaché de celui-ci. Le tissu conducteur (15) présente une forme plate et est enroulé autour de l'élément support d'électrode (112) et fixé à celui-ci.
PCT/JP2016/068791 2015-07-22 2016-06-24 Dispositif de détection de signal biologique Ceased WO2017013995A1 (fr)

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Cited By (3)

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JP2019051128A (ja) * 2017-09-15 2019-04-04 オムロンヘルスケア株式会社 電極ユニット、脈波測定ユニット、および脈波測定装置
JP2019201946A (ja) * 2018-05-24 2019-11-28 株式会社ｏｎｅＡ 睡眠状態測定装置
JPWO2020179845A1 (fr) * 2019-03-05 2020-09-10

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JP2007202939A (ja) * 2006-02-06 2007-08-16 Masafumi Matsumura 生体情報検出装置
JP2015083064A (ja) * 2013-10-25 2015-04-30 セイコーインスツル株式会社 生体情報検出装置
WO2015166752A1 (fr) * 2014-04-28 2015-11-05 株式会社村田製作所 Dispositif de détection de signal biologique

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2007202939A (ja) * 2006-02-06 2007-08-16 Masafumi Matsumura 生体情報検出装置
JP2015083064A (ja) * 2013-10-25 2015-04-30 セイコーインスツル株式会社 生体情報検出装置
WO2015166752A1 (fr) * 2014-04-28 2015-11-05 株式会社村田製作所 Dispositif de détection de signal biologique

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2019051128A (ja) * 2017-09-15 2019-04-04 オムロンヘルスケア株式会社 電極ユニット、脈波測定ユニット、および脈波測定装置
CN111093484A (zh) * 2017-09-15 2020-05-01 欧姆龙健康医疗事业株式会社 电极单元、脉波测定单元以及脉波测定装置
US11793414B2 (en) 2017-09-15 2023-10-24 Omron Corporation Electrode unit, pulse wave measurement unit, and pulse wave measurement device
JP2019201946A (ja) * 2018-05-24 2019-11-28 株式会社ｏｎｅＡ 睡眠状態測定装置
JP7222509B2 (ja) 2018-05-24 2023-02-15 株式会社oneA 睡眠状態測定装置
JPWO2020179845A1 (fr) * 2019-03-05 2020-09-10
WO2020179845A1 (fr) * 2019-03-05 2020-09-10 東レ株式会社 Outil d'acquisition de signal biologique
CN113498330A (zh) * 2019-03-05 2021-10-12 东丽株式会社 生物信号获取用具
JP7459862B2 (ja) 2019-03-05 2024-04-02 東レ株式会社 生体信号取得用具

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