WO2017033667A1 - 脈波測定装置 - Google Patents

脈波測定装置 Download PDF

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Publication number
WO2017033667A1
WO2017033667A1 PCT/JP2016/072354 JP2016072354W WO2017033667A1 WO 2017033667 A1 WO2017033667 A1 WO 2017033667A1 JP 2016072354 W JP2016072354 W JP 2016072354W WO 2017033667 A1 WO2017033667 A1 WO 2017033667A1
Authority
WO
WIPO (PCT)
Prior art keywords
pressure
pulse wave
semiconductor substrate
substrate
terminal
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/JP2016/072354
Other languages
English (en)
French (fr)
Japanese (ja)
Inventor
雄樹 加藤
教子 鴫原
祐之 若宮
小椋　敏彦
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.)
Omron Healthcare Co Ltd
Original Assignee
Omron Healthcare 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 Omron Healthcare Co Ltd filed Critical Omron Healthcare Co Ltd
Priority to CN201680047117.2A priority Critical patent/CN107920755B/zh
Priority to EP16839014.4A priority patent/EP3320834B1/en
Publication of WO2017033667A1 publication Critical patent/WO2017033667A1/ja
Priority to US15/893,438 priority patent/US20180160918A1/en
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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • 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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
    • 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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/02233—Occluders specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A61B5/681—Wristwatch-type devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal

Definitions

  • the present invention relates to a pulse wave measuring device.
  • a pressure type pressure measuring device that measures a contact pressure with an object to be measured by pressing the object to be measured is known.
  • a pulse wave measuring apparatus as an apparatus to which this pressing type pressure measuring apparatus is applied.
  • the pulse wave measuring device measures a pressure pulse wave by pressing a substrate having a pressure sensitive element against the body surface in order to measure a pressure pulse wave generated in an artery located relatively shallower than the skin in the living body.
  • Measuring the pressure pulse wave of a subject using such a pulse wave measuring device is very important for knowing the health condition of the subject.
  • Patent Document 1 is a document relating to this type of pressure-type pulse wave measuring device.
  • Patent Document 1 describes a pulse wave detection device on which a sensor chip having a diaphragm formed on a flat semiconductor substrate is mounted.
  • This sensor chip has a structure in which the pressure-sensitive element surface is protected by silicone rubber, and a portion of the silicone rubber surface that comes into contact with the living body is covered with conductive rubber.
  • the present invention has been made in view of the above circumstances. While reducing the thickness in the pressing direction, the influence of static electricity due to friction with the skin in repeated use is eliminated, and the detection accuracy of the pressure pulse wave is improved.
  • An object of the present invention is to provide a pulse wave measuring device that can be improved.
  • the pulse wave measuring device of the present invention includes a pressure sensitive element, a semiconductor substrate on which a first terminal portion electrically connected to the pressure sensitive element is formed, and electrically connected to the first terminal portion. And a hard substrate to which the semiconductor substrate is fixed, and a pressure pulse wave that is used when a pressure-sensitive surface on which the pressure-sensitive element is formed is pressed against a body surface of a living body A sensor, and a wiring board electrically connected to the second terminal portion, the flexible board to which the hard board is fixed, and an insulating material, covering the semiconductor substrate of the pressure pulse wave sensor A protective layer that protects the flexible substrate, wherein the flexible substrate includes an externally exposed terminal held at the same potential as the semiconductor substrate, and the terminal is in contact with the protective layer.
  • a pulse wave measuring device capable of improving the detection accuracy of a pressure pulse wave by reducing the influence of static electricity due to friction with the skin in repeated use while reducing the thickness in the pressing direction. Can be provided.
  • FIG. 2 is a schematic cross-sectional view showing a configuration in the vicinity of an interface between a semiconductor substrate 10A and a surface coating layer 15 of the pressure pulse wave sensor 1 of FIG.
  • FIG. 1 is a block diagram showing a configuration of a blood pressure measurement device 100 as a biological information measurement device for explaining an embodiment of the present invention.
  • the blood pressure measurement device 100 is, for example, a wrist-worn type that is worn on the wrist.
  • the blood pressure measurement device 100 functions as a pulse wave measurement device that measures a pulse wave from a living body.
  • the blood pressure measurement device 100 controls the pressure pulse wave sensor 1, a pressure mechanism 2 for pressing the pressure pulse wave sensor 1 against the body surface of the subject, and a signal output from the pressure pulse wave sensor 1. And a control unit 3 that calculates biological information including the blood pressure of the subject based on this signal.
  • FIG. 2 is a plan view of the flexible substrate 16 on which the pressure pulse wave sensor 1 shown in FIG. 1 is mounted.
  • the flexible substrate 16 has a rectangular shape whose longitudinal direction is a direction Y orthogonal to the direction X, which is one direction, and two pressure pulse wave sensors 1 and a connector 16C are mounted on the surface thereof. .
  • the two pressure pulse wave sensors 1 are arranged side by side in the direction Y.
  • the flexible substrate 16 is provided with wiring connected to the connection terminals of the two pressure pulse wave sensors 1 in a resin film. Each wiring is routed to the connector 16C.
  • the connector 16C and a connector of a circuit board (not shown) on which the control unit 3 and the like in FIG. 1 are formed are connected.
  • the flexible substrate 16 has through holes 16A and 16B substantially in the center of the region where each of the two pressure pulse wave sensors 1 is mounted.
  • terminals G1 which are a part of the wiring grounded via the circuit board connected to the connector 16C. G2 is exposed.
  • the terminal G1 and the terminal G2 are arranged at positions facing each other across the region between the two pressure pulse wave sensors 1 in the direction X.
  • FIG. 3 is a schematic sectional view taken along line AA shown in FIG.
  • FIG. 4 is a perspective view showing a main configuration of the pressure pulse wave sensor 1 viewed from the side in contact with the skin. In FIG. 4, illustration of some components is omitted. In FIG. 3, components other than the flexible substrate 16 constitute the pressure pulse wave sensor 1.
  • the pressure pulse wave sensor 1 includes a sensor chip 10 and a flat hard substrate 11 to which the sensor chip 10 is fixed.
  • the sensor chip 10 includes a semiconductor substrate 10A such as a silicon single crystal or a single crystal of a compound semiconductor such as gallium-arsenide.
  • the semiconductor substrate 10A has a rectangular shape in which the direction X is the longitudinal direction.
  • the hard substrate 11 is made of a material sufficiently higher in rigidity than the semiconductor substrate 10A such as a ceramic substrate or a glass substrate.
  • the hard substrate 11 has a rectangular shape in which the direction X is the longitudinal direction.
  • the surface of the semiconductor substrate 10A (surface on the side in contact with the skin of the living body) is composed of a bridge having four piezoresistive portions (strain gauges, strain gauges), and detects contact pressure.
  • a plurality of the pressure sensitive elements S are arranged along the direction X.
  • the plurality of pressure sensitive elements S arranged in the direction X constitute a pressure sensitive element row 10D.
  • illustration of the pressure sensitive element S is abbreviate
  • the surface opposite to the surface on which the pressure-sensitive element array 10 ⁇ / b> D is formed (hereinafter referred to as pressure-sensitive surface) is perpendicular to the pressure-sensitive surface (hereinafter referred to as sensor pressing direction).
  • a recess 10a that is recessed is formed.
  • the semiconductor substrate 10A is configured to have a thin portion (diaphragm) whose thickness in the sensor pressing direction is thinner than other portions due to the recess 10a.
  • column 10D is formed in the area
  • the portion excluding the recess 10a (in other words, the surface on which the recess 10a is formed) is fixed to the surface of the hard substrate 11 by the adhesive 12.
  • the adhesive 12 for example, a resin material such as an ultraviolet curable resin is used.
  • the semiconductor substrate 10A is fixed to the surface of the hard substrate 11 so that the recess 10a of the semiconductor substrate 10A communicates with the atmosphere only through the through hole 11D formed in the hard substrate 11.
  • One pressure pulse wave sensor 1 of the two pressure pulse wave sensors 1 of the blood pressure measurement device 100 is mounted on the flexible substrate 16 so that the through hole 11D and the through hole 16A overlap in a plan view viewed from the pressure-sensitive surface side. Is done.
  • the other of the two pressure pulse wave sensors 1 of the blood pressure measurement device 100 is mounted on the flexible substrate 16 so that the through hole 11D and the through hole 16B overlap in the same plan view. .
  • the space defined by the semiconductor substrate 10 ⁇ / b> A, the adhesive 12, and the hard substrate 11 is divided into the through hole 11 ⁇ / b> D of the hard substrate 11 and the through hole 16 ⁇ / b> A (or the through hole 16 ⁇ / b> B) of the flexible substrate 16.
  • the atmospheric pressure reference pressure
  • the first terminal portion 10B and the first terminal portion 10C that are electrically connected to the pressure-sensitive element array 10D are disposed at both ends in the direction X of the pressure-sensitive surface of the semiconductor substrate 10A.
  • the first terminal portion 10 ⁇ / b> B and the first terminal portion 10 ⁇ / b> C are each configured by a plurality of connection terminals arranged in a direction Y orthogonal to the direction X.
  • the second terminal portion 11B for electrical connection with the first terminal portion 10B and the first terminal portion 10C are electrically connected. And a second terminal portion 11C for the purpose.
  • the second terminal portion 11B, the first terminal portion 10B, the first terminal portion 10C, and the second terminal portion 11C are oriented in this order in a plan view as viewed from the direction perpendicular to the pressure-sensitive surface of the semiconductor substrate 10A.
  • X is arranged side by side.
  • the second terminal portion 11B and the second terminal portion 11C are each composed of a plurality of connection terminals arranged in a direction Y orthogonal to the direction X.
  • Each connection terminal of the second terminal portion 11B corresponds to one of the connection terminals of the first terminal portion 10B.
  • Each connection terminal of the second terminal portion 11C corresponds to one of the connection terminals of the first terminal portion 10C.
  • each connection terminal of the first terminal portion 10B and the corresponding connection terminal of the second terminal portion 11B are electrically connected by a wire W1 that is a first conductive member.
  • Each connection terminal of the first terminal portion 10C and the corresponding connection terminal of the second terminal portion 11C are electrically connected by a wire W2 that is a second conductive member.
  • the hard substrate 11 has a third terminal portion 16b made of a connection terminal connected to each connection terminal of the second terminal portion 11B via a wiring 16a, and each connection terminal of the second terminal portion 11C.
  • a third terminal portion 16d formed of a connection terminal connected via the wiring 16c is provided to be exposed on the surface opposite to the surface to which the semiconductor substrate 10A is fixed.
  • the third terminal portions 16 b and 16 d are connected to wiring terminals exposed from the resin film of the flexible substrate 16.
  • the wiring terminal of the flexible board 16 includes a terminal connected to the ground terminal of the circuit board connected via the connector 16C. That is, the flexible substrate 16 includes wiring that is held at the ground potential, and a part of the wiring that is exposed serves as the terminals G1 and G2 in FIG.
  • the wire W1 and the wire W2 are individually covered and protected by the protective member 13.
  • the protective member 13 for example, an epoxy resin or a silicone resin is used.
  • the semiconductor substrate 10A, the protective member 13 of the wire W1, the protective member 13 of the wire W2, and the hard substrate 11 are covered with a surface coating layer 15 which is a protective layer for protecting the surface of the pressure pulse wave sensor 1.
  • the surface coating layer 15 is made of an insulating material such as silicone resin.
  • the surface coating layer 15 is also formed on the mounting surface of the pressure pulse wave sensor 1 on the flexible substrate 16 so as to be in contact with at least a part of each of the terminal G1 and the terminal G2 exposed from the flexible substrate 16.
  • the surface coating layer 15 is preferably formed so as to completely cover each of the terminal G1 and the terminal G2.
  • the pressure pulse wave sensor 1 configured as described above has the pressure-sensitive element array 10D in a state where the pressure-sensitive element array 10D is located immediately above the artery and the direction X intersects (preferably orthogonally) the running direction of the artery.
  • the pressure-sensitive surface of the semiconductor substrate 10A on which 10D is formed is pressed against the body surface of the living body via the surface coating layer 15 and used. Thereby, from each pressure sensitive element S, an electrical signal corresponding to the strain applied to the thin portion of the semiconductor substrate 10A, that is, a signal representing a pressure fluctuation acting on the pressure sensitive element S is output.
  • the control unit 3 adjusts the pressing state of the pressure pulse wave sensor 1 on the body surface by the pressing mechanism 2, and based on the signal output from the pressure pulse wave sensor 1, the optimum pressure sensitive element After determining the optimum pressing force, the pressure pulse wave is measured based on the signal output from the optimum pressure-sensitive element at the optimum pressing force, and the biological information such as the blood pressure value and the pulse rate is obtained based on the pressure pulse wave. calculate.
  • FIG. 5 is an enlarged schematic sectional view of the vicinity of the interface between the sensor chip 10 and the surface coating layer 15.
  • the semiconductor substrate 10A of the sensor chip 10 is an N type, and a piezoresistive portion is constituted by a P type semiconductor layer formed on the semiconductor substrate 10A.
  • the negative charge 51 is generated in the surface coating layer 15 due to the friction between the surface coating layer 15 and the body surface, and the negative charge 51 is held at the interface between the surface coating layer 15 and the pressure-sensitive surface.
  • an inversion channel is formed by the positive charge 50 generated in the region between the piezoresistive portions (P + regions) in the semiconductor substrate 10A. This inversion channel gradually increases the offset voltage of the piezoresistor section.
  • the surface coating layer 15 is exposed from the flexible substrate 16 and is in contact with the terminals G1 and G2 held at the ground potential. For this reason, the negative charge which generate
  • the blood pressure measurement device 100 since it is not necessary to suppress the generation of static electricity due to friction, a configuration in which only the surface coating layer 15 is provided on the pressure-sensitive surface can be employed. For this reason, the distance between the pressure-sensitive surface and the skin of the living body can be minimized, and the pressure pulse wave detection accuracy can be improved.
  • the terminals G1 and G2 are formed separately from the second terminal portion 11B and the second terminal portion 11C, and the surface coating layer 15 and the terminals G1 and G2 are brought into contact with each other on the hard substrate 11. Is also possible.
  • the pressure pulse wave sensor 1 is further reduced in size, a sufficient space for forming the terminals G1 and G2 on the hard substrate 11 cannot be secured. Further, when the terminals G1 and G2 are formed on the hard substrate 11, wiring and terminals for holding the terminals G1 and G2 at the ground potential are added to the hard substrate 11, or terminals connected to the terminals are connected to the flexible substrate 16. This increases the manufacturing cost and the design layout. In particular, in the configuration having two pressure pulse wave sensors 1, it is necessary to additionally form terminals on each of the hard substrates 11 of the two pressure pulse wave sensors 1, resulting in a significant increase in cost.
  • the blood pressure measurement device 100 is a simple one in which the ground wiring generally included in the flexible substrate 16 is exposed to be terminals G1 and G2, and the terminals G1 and G2 are covered with the surface coating layer 15. It is a simple configuration. Therefore, the manufacturing cost does not increase and the design layout is not complicated. Further, the pressure pulse wave sensor 1 can be easily downsized.
  • terminals G1 and G2 are arranged in the direction X across the region between the two pressure pulse wave sensors 1.
  • the surface coating layer 15 can be grounded at an approximately equal distance from the pressure-sensitive surfaces of the two pressure pulse wave sensors 1, and the offset voltages of the two pressure pulse wave sensors 1 can be controlled in substantially the same manner. .
  • a wrist-mounted blood pressure measuring device that detects a pressure pulse wave of the radial artery of the wrist has been described, but it may be applied to the carotid artery or the dorsal artery.
  • the blood pressure measurement device 100 has two pressure pulse wave sensors 1. However, if there is at least one pressure pulse wave sensor 1, it is possible to detect the pressure pulse wave and measure biological information. is there.
  • the semiconductor substrate 10A is held at the ground potential and the terminals G1 and G2 are held at the ground potential.
  • the semiconductor substrate 10A and the surface coating layer 15 can be at the same potential, the semiconductor substrate It is possible to prevent negative charges from being held at the interface between 10A and the surface coating layer 15. For this reason, the holding potential of the semiconductor substrate 10A may not be the ground potential.
  • the terminals G1 and G2 may be held at this predetermined potential.
  • the disclosed pulse wave measuring device includes a pressure sensitive element, a semiconductor substrate on which a first terminal portion electrically connected to the pressure sensitive element is formed, and electrically connected to the first terminal portion. And a hard substrate to which the semiconductor substrate is fixed, and a pressure pulse wave that is used when a pressure-sensitive surface on which the pressure-sensitive element is formed is pressed against a body surface of a living body A sensor, and a wiring board electrically connected to the second terminal portion, the flexible board to which the hard board is fixed, and an insulating material, covering the semiconductor substrate of the pressure pulse wave sensor A protective layer that protects the flexible substrate, wherein the flexible substrate includes an externally exposed terminal held at the same potential as the semiconductor substrate, and the terminal is in contact with the protective layer.
  • the semiconductor substrate of the pressure pulse wave sensor includes a pressure sensitive element array including a plurality of pressure sensitive elements arranged in one direction, and the pressure sensitive element array and the electrical
  • the pressure pulse wave sensor has a pressure-sensitive surface on which the pressure-sensitive element array is formed in a state where the one direction intersects the traveling direction of the living artery.
  • the pressure sensor is used by being pressed against the body surface of the living body, and the two pressure pulse wave sensors are fixed to the flexible substrate side by side in a direction orthogonal to the one direction, and has two terminals. The two terminals are arranged at positions facing each other across the region between the two pressure pulse wave sensors in the one direction.
  • a pulse wave measuring device capable of improving the detection accuracy of a pressure pulse wave by reducing the influence of static electricity due to friction with the skin in repeated use while reducing the thickness in the pressing direction. Can be provided.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Medical Informatics (AREA)
  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Public Health (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Vascular Medicine (AREA)
  • Physiology (AREA)
  • Signal Processing (AREA)
  • Ophthalmology & Optometry (AREA)
  • Artificial Intelligence (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Psychiatry (AREA)
  • Dentistry (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
PCT/JP2016/072354 2015-08-24 2016-07-29 脈波測定装置 Ceased WO2017033667A1 (ja)

Priority Applications (3)

Application Number Priority Date Filing Date Title
CN201680047117.2A CN107920755B (zh) 2015-08-24 2016-07-29 脉搏波测定装置
EP16839014.4A EP3320834B1 (en) 2015-08-24 2016-07-29 Pulse wave measurement device
US15/893,438 US20180160918A1 (en) 2015-08-24 2018-02-09 Pulse wave measurement device

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2015-164696 2015-08-24
JP2015164696A JP6524858B2 (ja) 2015-08-24 2015-08-24 脈波測定装置

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US15/893,438 Continuation US20180160918A1 (en) 2015-08-24 2018-02-09 Pulse wave measurement device

Publications (1)

Publication Number Publication Date
WO2017033667A1 true WO2017033667A1 (ja) 2017-03-02

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PCT/JP2016/072354 Ceased WO2017033667A1 (ja) 2015-08-24 2016-07-29 脈波測定装置

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US (1) US20180160918A1 (enExample)
EP (1) EP3320834B1 (enExample)
JP (1) JP6524858B2 (enExample)
CN (1) CN107920755B (enExample)
WO (1) WO2017033667A1 (enExample)

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Publication number Priority date Publication date Assignee Title
CN110255491A (zh) * 2019-06-27 2019-09-20 中国科学院微电子研究所 Mems压力传感器封装结构及封装方法
CN115227223A (zh) * 2022-06-06 2022-10-25 杭州回车电子科技有限公司 脉搏波传感器装置

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EP3320834B1 (en) 2023-06-07
EP3320834A4 (en) 2019-03-27
JP2017042206A (ja) 2017-03-02
JP6524858B2 (ja) 2019-06-05
EP3320834A1 (en) 2018-05-16
CN107920755B (zh) 2021-08-31
CN107920755A (zh) 2018-04-17
US20180160918A1 (en) 2018-06-14

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