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WO2025182381A1 - Tampon pour capteur de pression et dispositif de mesure de pression - Google Patents

Tampon pour capteur de pression et dispositif de mesure de pression

Info

Publication number
WO2025182381A1
WO2025182381A1 PCT/JP2025/002348 JP2025002348W WO2025182381A1 WO 2025182381 A1 WO2025182381 A1 WO 2025182381A1 JP 2025002348 W JP2025002348 W JP 2025002348W WO 2025182381 A1 WO2025182381 A1 WO 2025182381A1
Authority
WO
WIPO (PCT)
Prior art keywords
pressure sensor
pressure
pad
blood pressure
region
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.)
Pending
Application number
PCT/JP2025/002348
Other languages
English (en)
Japanese (ja)
Inventor
賀東 張
旻玉 李
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.)
Tokai National Higher Education and Research System NUC
Original Assignee
Tokai National Higher Education and Research System NUC
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 Tokai National Higher Education and Research System NUC filed Critical Tokai National Higher Education and Research System NUC
Publication of WO2025182381A1 publication Critical patent/WO2025182381A1/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

Links

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
    • 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

Definitions

  • the technology disclosed in this specification relates to a pressure sensor pad for pressing a pressure sensor against an object to measure changes in the pressure of the object over time.
  • a wristwatch-type blood pressure measurement device that is worn on a person's wrist to measure blood pressure values has been proposed (see, for example, Patent Document 1).
  • This blood pressure measurement device is equipped with a pressure sensor that uses, for example, a piezoelectric element.
  • Conventional blood pressure measurement devices are equipped with a cuff (arm cuff) to compress the artery.
  • a cuff arm cuff
  • the presence of the cuff tends to make the device relatively large.
  • compression of the artery by the cuff can easily cause the user to feel a sense of pressure and strain on the heart.
  • conventional blood pressure measurement devices have the problem of requiring a cuff to accurately measure blood pressure.
  • this issue is not limited to blood pressure measurement devices, but is a common issue with pressure measurement devices equipped with pressure sensors for measuring changes in the pressure of an object over time.
  • the pressure sensor pad disclosed in this specification is used to press a pressure sensor against an object to measure changes in the pressure of the object over time.
  • the pressure sensor pad is formed from a porous material with an elastic modulus of 0.1 MPa or less.
  • the thickness of the pressure sensor pad is 3 mm or more and 10 mm or less. This pressure sensor pad allows the pressure sensor to accurately measure changes in the pressure of the object over time without using a cuff.
  • the thickness of the pressure sensor pad may be 5 mm or more and 10 mm or less.
  • the compressive stress-compressive strain curve of the porous body may be divided by two inflection points on the curve and include a first region, a second region, and a third region arranged in order of increasing compressive strain, and the porous body may be in the first region or the second region when a preload of 0.5 N or more and 1.5 N or less is applied. This configuration allows the pressure sensor to measure changes in the pressure of an object over time with even greater accuracy.
  • the pressure of the object may be blood pressure.
  • the pressure sensor can accurately measure changes in blood pressure over time.
  • the pressure measuring device disclosed in this specification comprises the pressure sensor pad and the pressure sensor pressed against the object by the pressure sensor pad. With this configuration, it is possible to accurately measure changes in the pressure of the object over time using the pressure sensor pressed against the object by the pressure sensor pad, without using a cuff.
  • the pressure sensor may be configured to include a piezoelectric element. With this configuration, it is possible to measure changes in the pressure of an object over time with the same accuracy as when a capacitance-type pressure sensor is used.
  • the technology disclosed in this specification can be realized in various forms, such as a pressure sensor pad, a pressure measuring device equipped with a pressure sensor and a pressure sensor pad, a method of manufacturing or using a pressure measuring device, etc.
  • FIG. 1 is an explanatory diagram showing the configuration of a blood pressure measurement device 100 according to an embodiment of the present invention.
  • FIG. 1 is an explanatory diagram showing a state in which the blood pressure measurement device 100 of the present embodiment is worn.
  • FIG. 1 is an illustration showing a typical compressive stress-compressive strain curve for the foamed hyperelastic material used to form the pad 10.
  • FIG. 1 is an explanatory diagram showing an example of changes over time in blood pressure values BP measured by the blood pressure measurement device 100.
  • FIG. 10 is an explanatory diagram showing the evaluation results of the measurement accuracy of the pressure pulse wave when the thickness t of the pad 10 and the preload PP applied to the pad 10 are varied for the sample SA1.
  • FIG. 10 is an explanatory diagram showing the evaluation results of the measurement accuracy of the pressure pulse wave when the thickness t of the pad 10 and the preload PP applied to the pad 10 are varied for sample SA2.
  • FIG. 10 is an explanatory diagram showing the evaluation results of the measurement accuracy of the pressure pulse wave when the thickness t of the pad 10 and the preload PP applied to the pad 10 are varied for sample SA2.
  • FIG. 1 is an explanatory diagram showing the configuration of a blood pressure measurement device 100 according to this embodiment.
  • Fig. 2 is an explanatory diagram showing the blood pressure measurement device 100 according to this embodiment in a worn state.
  • the blood pressure measurement device 100 of this embodiment is a device for measuring a person's blood pressure. As shown in FIG. 2, the blood pressure measurement device 100 is worn on the person's wrist WP and measures the blood pressure for each beat according to the tonometry method using a pressure sensor 20 pressed against the radial artery BV running on the radius RA near the body surface SU.
  • the blood pressure measurement device 100 is an example of a pressure measurement device.
  • the blood pressure measurement device 100 includes a band 40, a main body 30, a pressure sensor 20, and a pressure sensor pad (hereinafter simply referred to as "pad") 10.
  • the band 40 is a belt-like member for securing the blood pressure measurement device 100 to a person's wrist WP.
  • the main body 30 and pad 10 are attached to the band 40.
  • the main body unit 30 is the part that controls the entire blood pressure measurement device 100.
  • the main body unit 30 has, for example, an integrated circuit, a display, a communication interface, and a battery that supplies power to each part.
  • the main body unit 30 communicates with the pressure sensor 20 and other devices via the communication interface in accordance with a communication standard such as Bluetooth (registered trademark).
  • the main body unit 30 also displays various images on the display. In the example of Figure 1, the display of the main body unit 30 displays images showing the time (16:08), blood pressure values (systolic blood pressure 117, diastolic blood pressure 71), blood glucose level (81), pulse (76), health condition (good), and remaining battery power.
  • the pressure sensor 20 is a sensor for measuring changes in pressure over time. It is equipped with a piezoelectric element that outputs a voltage signal corresponding to the force (pressure).
  • a pressure sensor 20 is used in which a PZT (lead zirconate titanate) film is formed as a piezoelectric element on a flexible substrate.
  • the PZT film thickness is, for example, 2 ⁇ m.
  • the pad 10 is interposed between the band 40 or main body 30 and the pressure sensor 20, and is a component for pressing the pressure sensor 20 against the person's wrist WP.
  • the presence of the pad 10 allows the blood pressure measurement device 100 to measure blood pressure and other biological information with high accuracy without using a cuff.
  • the pad 10 is a porous body, and is formed, for example, from a foamed superelastic material. Examples of materials that can be used to form the pad 10 include polyurethane sponge, melamine sponge, and ethylene propylene diene rubber sponge.
  • the pad 10 is substantially flat and rectangular in plan view. The width and height of the pad 10 are, for example, 10 mm or more and 30 mm or less, and may be 15 mm or more and 25 mm or less.
  • FIG. 3 is an explanatory diagram showing a typical compressive stress-compressive strain curve of the foamed hyperelastic material used to form the pad 10.
  • This compressive stress-compressive strain curve includes a first region R1, in which the compressive strain ⁇ increases approximately linearly with increasing compressive stress ⁇ ; a second region R2, continuous with the first region R1, in which the compressive strain ⁇ increases at a substantially constant compressive stress ⁇ ; and a third region R3, continuous with the second region R2, in which the compressive stress ⁇ increases more rapidly than in the first region R1.
  • the material deforms linearly elastically due to bending of the porous walls.
  • the porous walls deform significantly.
  • the second region R2 is also called the plateau region.
  • Each region in the compressive stress-compressive strain curve is defined by an inflection point POI, where the second derivative of the curve becomes zero.
  • the attachment positions of the pressure sensor 20 and pad 10 on the band 40 are set so that the pressure sensor 20 and pad 10 are positioned over the radial artery BV when the blood pressure measurement device 100 is attached to a person's wrist WP.
  • the pressure sensor 20 outputs a voltage signal indicating changes over time (pressure pulse waves) in the internal pressure (i.e., blood pressure) of the radial artery BV to the main body 30.
  • the main body 30 converts the voltage signal output from the pressure sensor 20 into a blood pressure value. This enables the blood pressure measurement device 100 to measure the blood pressure value.
  • the radial artery BV is an example of an object whose pressure is measured by the pressure sensor 20.
  • Figure 4 is an explanatory diagram showing an example of changes in blood pressure BP over time measured by blood pressure measurement device 100.
  • Figure 4 shows changes in blood pressure BP over time during a period To equivalent to one cardiac beat.
  • the curve showing changes in blood pressure BP over time has a shape in which the ejection wave Ws, the reflected wave (tidal wave) Wt, and the dicrotic wave Wd are arranged in this order.
  • the ejection wave Ws and the reflected wave Wt are observed during the systolic period T1 of the heart, which corresponds to the first half of the pulse, and the dicrotic wave Wd is observed during the diastolic period T2 of the heart, which corresponds to the second half of the pulse.
  • the blood pressure P0 at the start of the pulse is the minimum blood pressure
  • the blood pressure P1 at the peak of the ejection wave Ws is the maximum blood pressure.
  • the shape of the curve showing changes in blood pressure BP over time is determined by factors such as the pulsation of the heart, the opening and closing of valves, the hardening of blood vessels, and the viscosity of blood flow.
  • the blood pressure measuring device 100 of this embodiment displays blood pressure, blood glucose levels, pulse rate, and health status on the display of the main unit 30 based on the measurement results from the pressure sensor 20.
  • the pad 10 of this embodiment is formed from a porous body with an elastic modulus of 0.1 MPa or less.
  • the elastic modulus of the material forming the pad 10 may be 0.08 MPa or less, 0.05 MPa or less, or 0.01 MPa or less.
  • the elastic modulus of the material forming the pad 10 is the slope of the linear portion in the first region R1 of the compressive stress-compressive strain curve shown in Figure 3. When a preload of 0.5 N or more and 1.5 N or less is applied, the pad 10 is in the state of the first region R1 or the second region R2 of the compressive stress-compressive strain curve.
  • the thickness t of the pad 10 is 0.5 mm or more and 20 mm or less.
  • the thickness t of the pad 10 may be 1 mm or more and 15 mm or less, 3 mm or more and 10 mm or less, 5 mm or more and 9 mm or less, or 6 mm or more and 8 mm or less.
  • FIG. 5 is an explanatory diagram showing the configuration of an experimental device 200 used in the performance evaluation.
  • the experimental device 200 includes a test stand 210, a force gauge 220, a charge amplifier 230, and an oscilloscope 240.
  • a person's hand HH was placed on the test stand 210, with the pressure sensor 20 placed against the wrist.
  • a sample of the pad 10 was then placed on top of the test stand 210, and a preload was applied to the pad 10, pressing the pressure sensor 20 against the person's wrist.
  • a waveform showing the time-dependent change in blood pressure (pressure pulse wave) measured by the pressure sensor 20 was read using the oscilloscope 240.
  • Fig. 6 is a graph showing pressure pulse waves measured by the experimental device 200.
  • Fig. 6 shows pressure pulse waves measured when a preload of 0.5 N was applied to the pad 10 for multiple samples SA1 to SA8 made of different materials.
  • the materials used for each sample are as follows: Sample SA1: Ethylene propylene diene rubber foam Sample SA2: Ethylene propylene diene rubber sponge (closed cell) Sample SA3: Polyurethane sponge (open cell) Sample SA4: Melamine sponge (net type) Sample SA5: Polyurethane sponge Sample SA6: Ultra-low hardness urethane sheet Sample SA7: Special pore polyurethane sponge Sample SA8: Chloroprene rubber sponge
  • samples SA1 to SA5 clearly show the waveform of a pressure pulse wave having an ejection wave Ws, a reflected wave Wt, and a dicrotic wave Wd. Therefore, if the materials used to form these samples are used to fabricate pad 10, it can be said that the accuracy of pressure measurement by pressure sensor 20 will be improved.
  • samples SA1, SA3, and SA5 show the waveform of a pressure pulse wave extremely clearly. Therefore, if the materials used to fabricate pad 10 are used to fabricate pad 10, it can be said that the accuracy of pressure measurement by pressure sensor 20 will be further improved.
  • Figure 7 is a graph showing the measurement results of the compressive stress-compressive strain curves for samples SA1 to SA4. As shown in Figure 7, all of samples SA1 to SA4 have an elastic modulus E of 0.1 MPa or less. Furthermore, all of samples SA1 to SA4 are in the first region R1 or the second region R2 on the compressive stress-compressive strain curve when a preload of 0.5 N or more and 1.5 N or less is applied.
  • Figure 8 is a graph showing the measurement results of the compressive stress-compressive strain curve for sample SA1 when the thickness t of the pad 10 is varied. As shown in Figure 8, for sample SA1, regardless of whether the thickness t is 1 mm, 5 mm, or 10 mm, when a preload of 0.5 N or more and 1.5 N or less is applied, the compressive stress-compressive strain curve is in the first region R1 or the second region R2.
  • Figure 9 is a graph showing the measurement results of the compressive stress-compressive strain curve for sample SA2 when the thickness t of the pad 10 is varied. As shown in Figure 9, for sample SA2, regardless of whether the thickness t is 1 mm, 5 mm, or 10 mm, when a preload of 0.5 N or more and 1.5 N or less is applied, the compressive stress-compressive strain curve is in the first region R1 or the second region R2.
  • FIG. 10 is a graph showing the pressure pulse wave for sample SA1 when the thickness t of the pad 10 and the preload PP applied to the pad 10 are varied.
  • FIG. 11 is an explanatory diagram showing the evaluation results of the measurement accuracy of the pressure pulse wave for sample SA1 when the thickness t of the pad 10 and the preload PP applied to the pad 10 are varied. As shown in FIGS.
  • Figure 12 is a graph showing the pressure pulse wave for sample SA2 when the thickness t of the pad 10 and the preload PP applied to the pad 10 are varied.
  • Figure 13 is an explanatory diagram showing the evaluation results of the measurement accuracy of the pressure pulse wave for sample SA2 when the thickness t of the pad 10 and the preload PP applied to the pad 10 are varied.
  • Figure 14 is a graph showing the measurement accuracy of pressure pulse waves by a pressure sensor.
  • Figure 14 shows the pressure pulse waves measured by pressure sensor 20 of this embodiment and pressure sensor 20X of the comparative example.
  • Pressure sensor 20 of this embodiment has a PZT film formed as a piezoelectric element on a flexible substrate.
  • Pressure sensor 20X of the comparative example is a capacitance-type pressure sensor (FS1M-5NP manufactured by THK PRECISION).
  • the pressure pulse waves measured by the two pressure sensors 20, 20X are nearly identical (correlation coefficient: 0.99), confirming that pressure sensor 20 of this embodiment has measurement accuracy comparable to that of capacitance-type pressure sensor 20X.
  • the pad 10 of this embodiment is used to press the pressure sensor 20 against the human body to measure changes in blood pressure over time, and is made of a porous material with an elastic modulus of 0.1 MPa or less, and has a thickness t of 3 mm to 10 mm.
  • the pad 10 of this embodiment allows the pressure sensor 20 to accurately measure changes in blood pressure over time without using a cuff.
  • the thickness t of the pad 10 of this embodiment is 5 mm or more and 10 mm or less.
  • the pad 10 of this embodiment allows the pressure sensor 20 to measure changes in blood pressure over time with even greater accuracy.
  • the compressive stress-compressive strain curve of the porous body used to form the pad 10 of this embodiment is divided by two inflection points POI of the curve and includes a first region R1, a second region R2, and a third region R3, arranged in order of increasing compressive strain.
  • a preload of 0.5 N or more and 1.5 N or less is applied to the pad 10, it is in the state of the first region R1 or the second region R2.
  • the pressure sensor 20 can measure changes in blood pressure over time with even greater accuracy.
  • the blood pressure measurement device 100 of this embodiment includes a pad 10 and a pressure sensor 20 that is pressed against the human body by the pad 10. With the blood pressure measurement device 100 of this embodiment, changes in blood pressure over time can be measured with high accuracy by the pressure sensor 20 that is pressed against the human body by the pad 10, without using a cuff.
  • the pressure sensor 20 is equipped with a piezoelectric element.
  • the blood pressure measurement device 100 of this embodiment can measure changes in blood pressure over time with the same accuracy as when a capacitance-type pressure sensor is used.
  • the configuration of the blood pressure measurement device 100 in the above embodiment is merely an example and can be modified in various ways.
  • the shape and material of the pad 10 are merely an example and can be modified in various ways.
  • the pressure sensor 20 is pressed against the wrist using the pad 10 to measure pressure, but the location where blood pressure is measured using the pressure sensor 20 is not limited to the wrist and may be other parts of the human body such as the neck, feet, or ears.
  • the pad 10 was applied to a blood pressure measurement device 100.
  • the pad 10 disclosed in this specification is not limited to blood pressure measurement devices and can be used in general applications in which a pressure sensor is pressed against an object to measure changes in the pressure of the object over time.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Medical Informatics (AREA)
  • Physics & Mathematics (AREA)
  • Vascular Medicine (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Veterinary Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physiology (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Ophthalmology & Optometry (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

La présente invention mesure avec précision un changement de pression dans le temps sur un objet avec un capteur de pression sans utiliser de brassard. Ce tampon pour capteur de pression est destiné à presser, contre un objet, un capteur de pression pour mesurer un changement dans le temps de la pression sur l'objet, et est formé à partir d'un corps poreux ayant un coefficient élastique inférieur ou égal à 0,1 MPa. L'épaisseur du tampon pour capteur de pression est de 3 mm à 10 mm.
PCT/JP2025/002348 2024-02-28 2025-01-27 Tampon pour capteur de pression et dispositif de mesure de pression Pending WO2025182381A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2024-028019 2024-02-28
JP2024028019A JP2025130757A (ja) 2024-02-28 2024-02-28 圧力センサ用パッドおよび圧力測定装置

Publications (1)

Publication Number Publication Date
WO2025182381A1 true WO2025182381A1 (fr) 2025-09-04

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ID=96920353

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2025/002348 Pending WO2025182381A1 (fr) 2024-02-28 2025-01-27 Tampon pour capteur de pression et dispositif de mesure de pression

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JP (1) JP2025130757A (fr)
WO (1) WO2025182381A1 (fr)

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2005516656A (ja) * 2002-02-05 2005-06-09 テンシス メディカル インコーポレイテッド パラメトリックスを使用して血行力学パラメータを非侵襲的に測定するための方法および装置
US20090177096A1 (en) * 2008-01-04 2009-07-09 Samsung Electronics Co., Ltd. Contact force sensor package, blood pressure meter with the same, and method for fabricating the contact force sensor package
WO2016121399A1 (fr) * 2015-01-29 2016-08-04 京セラ株式会社 Dispositif de mesure et système de capteur
US20160287102A1 (en) * 2015-04-02 2016-10-06 Microsoft Technology Licensing, Llc Transducing pressure to a non-invasive pulse sensor
KR20190088784A (ko) * 2018-01-19 2019-07-29 한국과학기술원 인체 상에 부착 가능한 압전 맥박 소자를 이용한 압전 기반 혈압 측정 장치
CN114190901A (zh) * 2021-11-08 2022-03-18 黑龙江大学 一种脉搏传感器及其集成化工艺方法

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2005516656A (ja) * 2002-02-05 2005-06-09 テンシス メディカル インコーポレイテッド パラメトリックスを使用して血行力学パラメータを非侵襲的に測定するための方法および装置
US20090177096A1 (en) * 2008-01-04 2009-07-09 Samsung Electronics Co., Ltd. Contact force sensor package, blood pressure meter with the same, and method for fabricating the contact force sensor package
WO2016121399A1 (fr) * 2015-01-29 2016-08-04 京セラ株式会社 Dispositif de mesure et système de capteur
US20160287102A1 (en) * 2015-04-02 2016-10-06 Microsoft Technology Licensing, Llc Transducing pressure to a non-invasive pulse sensor
KR20190088784A (ko) * 2018-01-19 2019-07-29 한국과학기술원 인체 상에 부착 가능한 압전 맥박 소자를 이용한 압전 기반 혈압 측정 장치
CN114190901A (zh) * 2021-11-08 2022-03-18 黑龙江大学 一种脉搏传感器及其集成化工艺方法

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