WO2018066680A1 - Dispositif de mesure, méthode de mesure et programme - Google Patents

Dispositif de mesure, méthode de mesure et programme Download PDF

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Publication number
WO2018066680A1
WO2018066680A1 PCT/JP2017/036396 JP2017036396W WO2018066680A1 WO 2018066680 A1 WO2018066680 A1 WO 2018066680A1 JP 2017036396 W JP2017036396 W JP 2017036396W WO 2018066680 A1 WO2018066680 A1 WO 2018066680A1
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WIPO (PCT)
Prior art keywords
pressing force
unit
measurement
test site
control unit
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PCT/JP2017/036396
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English (en)
Japanese (ja)
Inventor
正太郎 杉田
杤久保　修
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京セラ株式会社
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Publication of WO2018066680A1 publication Critical patent/WO2018066680A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—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 pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—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
    • A61B5/0225—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers the pressure being controlled by electric signals, e.g. derived from Korotkoff sounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0285—Measuring or recording phase velocity of blood waves

Definitions

  • the present disclosure relates to a measurement apparatus, a measurement method, and a program.
  • the measuring device includes an output unit, a pressing force adjustment unit, and a control unit.
  • the output unit outputs a signal based on scattered light from a region to be examined.
  • the said pressing force adjustment part adjusts the pressing force with respect to the said test site
  • the said control part controls the said pressing force with respect to the said test
  • the measurement method outputs a signal based on the scattered light from the test site, and controls the pressing force applied to the test site by the pressing force adjusting unit based on the signal.
  • the program causes a computer to output a signal based on scattered light from the test site, and controls the pressing force applied to the test site by the pressing force adjusting unit based on the signal.
  • FIG. 1 It is a figure showing an example of a wearing state of a measuring device concerning a 1st embodiment of this indication. It is sectional drawing of the sensor part of the measuring apparatus shown in FIG. It is a functional block diagram which shows an example of schematic structure of the measuring apparatus of FIG. It is a figure which shows an example of the power spectrum produced
  • FIG. 1 is a diagram illustrating an example of a mounting state of the measurement apparatus according to the first embodiment of the present disclosure.
  • the measuring apparatus 100 shown in FIG. 1 is used in a state where a subject is worn on the head.
  • the measuring apparatus 100 acquires a biometric output based on scattered light while being in contact with the test site, and calculates biometric information from the acquired biometric output.
  • the measuring apparatus 100 according to an embodiment calculates the average blood pressure of the subject as the biological information.
  • the measuring apparatus 100 includes a head mounting unit 110 and a sensor unit 120 attached to the head mounting unit 110.
  • the head mounting unit 110 is a mounting tool for the subject to mount the measuring apparatus 100 on the head.
  • the head mounting unit 110 includes a head circumference holding unit 111 that holds the periphery of the head (head circumference), and a head top holding unit 112 that sandwiches the head of the subject from the left and right across the top of the head.
  • the head circumference holding unit 111 is configured by a member having elasticity such as rubber.
  • the head holding part 112 is configured by a member having rigidity such as stainless steel or carbon fiber.
  • the subject wears the head wearing part 110 from the top of the head.
  • the mounting state of the head mounting unit 110 is maintained (fixed) by the head circumference holding unit 111 holding the head circumference.
  • the head mounting part 110 is not limited to the form shown in FIG.
  • the head mounting part 110 may be in any form that can be worn by the subject, such as a hat shape.
  • the sensor unit 120 acquires scattered light from the test site while in contact with the test site of the subject.
  • the test site is a temple.
  • the sensor unit 120 acquires scattered light from the superficial temporal artery while in contact with the subject's temple.
  • the sensor unit 120 is attached to one end of the crown holding unit 112, for example.
  • the sensor unit 120 is disposed at a position where the subject contacts the temple when the subject wears the measuring apparatus 100.
  • FIG. 2 is a cross-sectional view of the sensor unit 120 in the measuring apparatus 100 shown in FIG.
  • FIG. 2 is a cross-sectional view showing a state in which the sensor unit 120 is in contact with the test site.
  • the sensor unit 120 includes a biological sensor 121, a pressure sensor 122, a pressing force adjustment unit 123, and an air cuff 124.
  • the biosensor 121, the pressure sensor 122, the pressing force adjustment unit 123, and the air cuff 124 are arranged (stacked) in this order to constitute the sensor unit 120.
  • the biological sensor 121 acquires scattered light in a state where it is in contact with the region to be examined.
  • the biosensor 121 functions as an output unit that outputs a signal based on the acquired scattered light.
  • the biosensor 121 includes a light emitting unit and a light receiving unit, for example, and details of the biosensor 121 will be described later.
  • the biosensor 121 is supported by a biosensor support unit 126, for example.
  • the pressure sensor 122 measures the pressure applied to the measuring device 100 from the test site.
  • the pressure sensor 122 outputs pressure as an electrical signal. That is, the pressure sensor 122 outputs the pressure in units of voltage (for example, mV).
  • the pressure sensor 122 is supported by the pressure sensor support portion 127.
  • the pressure sensor support 127 is configured with a member and a structure that can support the pressure sensor 122 so that the position of the pressure sensor 122 is not displaced by the pressure from the test site.
  • the pressure sensor support 127 is made of, for example, a hard aluminum plate.
  • the pressure sensor support part 127 is disposed between the pressure sensor 122 and the pressing force adjustment part 123, for example.
  • the pressure sensor support part 127 makes it difficult for the position of the pressure sensor 122 to be displaced, making it easier to accurately measure the pressure from the site to be examined.
  • the pressing force adjusting unit 123 is a member that can adjust the pressing force applied to the test site by the measuring apparatus 100.
  • the pressing force adjusting unit 123 presses the test site via the biosensor 121 with a pressing force controlled by the control unit described later.
  • the pressing force adjustment unit 123 may be an actuator, for example.
  • the pressing force adjusting unit 123 may be, for example, a sheet-like conductive polymer actuator. When a voltage is applied to the conductive polymer actuator, ions move in the internal electrolyte layer, and the molecules in the vicinity of the electrode swell and physically deform.
  • the conductive polymer actuator adjusts the pressing force on the test site by changing the thickness in the arrangement direction of each member of the sensor unit 120.
  • various actuators such as a solenoid actuator that uses the force of an electromagnet, a motor that uses a motor, or that that uses hydraulic pressure or the like can be used.
  • the air cuff 124 measures the pressure applied to the measuring device 100 from the test site and outputs the pressure in units of pressure (for example, mmHg).
  • the air cuff 124 is a sheet-like cuff filled with air.
  • the air cuff 124 is used for calibration of the pressure sensor 122.
  • the calibration here refers to a process of associating the voltage value output by the pressure sensor 122 with the pressure value measured by the air cuff 124. Specifically, the voltage value output by the pressure sensor 122 is converted into a pressure value. This refers to the process of determining the criteria for conversion to. If calibration by the pressure sensor 122 is not required, the sensor unit 120 may not include the air cuff 124.
  • the air cuff 124 is supported by the support plate 125.
  • the support plate 125 is a plate member having rigidity.
  • the support plate 125 is coupled to the crown holding part 112.
  • the sensor unit 120 may not include the support plate 125, and the crown holding unit 112 may function as the support plate 125.
  • the sensor unit 120 is easily connected to the rigid support plate 125 or the crown holding unit 112, so that the wearing state with respect to the subject is easily maintained in a constant state (position). As a result, a measurement error of biological information by the measurement apparatus 100 is less likely to occur.
  • FIG. 3 is a functional block diagram showing an example of a schematic configuration of the measuring apparatus 100 of FIG.
  • the measuring apparatus 100 includes a sensor unit 120, a control unit 130, an input unit 140, a notification unit 150, and a storage unit 160.
  • the input unit 140, the notification unit 150, and the storage unit 160 may be provided in the head mounting unit 110, for example, or may be provided in a device separate from the head mounting unit 110.
  • the input unit 140, the notification unit 150, and the storage unit 160 may be provided in a terminal device that can communicate with the sensor unit 120 by wire or wireless, for example.
  • the terminal device may include a control unit that executes a part of the biological information measurement function by the control unit 130, for example.
  • the control unit 130 is a processor that controls and manages the entire measurement apparatus 100 including each functional block of the measurement apparatus 100.
  • the control unit 130 includes a processor such as a CPU (Central Processing Unit) that executes a program that defines a control procedure.
  • a program is stored in, for example, the storage unit 160 or an external storage medium connected to the measurement apparatus 100.
  • the measuring device 100 includes at least one processor 130a to provide control and processing capabilities to perform various functions, as will be described in more detail below.
  • At least one processor 130a may be implemented as a single integrated circuit (IC) or as a plurality of communicatively connected integrated circuit ICs and / or discrete circuits. Also good.
  • the at least one processor 130a can be implemented according to various known techniques.
  • the processor 130a includes one or more circuits or units configured to perform one or more data calculation procedures or processes, for example, by executing instructions stored in associated memory.
  • processor 130a may be firmware (eg, a discrete logic component) configured to perform one or more data computation procedures or processes.
  • processor 130a may include one or more processors, controllers, microprocessors, microcontrollers, application specific integrated circuits (ASICs), digital signal processors, programmable logic devices, field programmable gate arrays, or the like.
  • ASICs application specific integrated circuits
  • the functions of the control unit 130 described below may be executed including any combination of these devices or configurations, or other known devices or combinations of configurations.
  • the control unit 130 controls the pressing force adjustment unit 123 based on the scattered light acquired by the biological sensor 121.
  • the control unit 130 controls the pressing force from the measuring apparatus 100 to the test site under the control of the pressing force adjusting unit 123.
  • the control unit 130 controls the pressing force so as to suppress the change in the blood vessel diameter at the test site. Details of the control of the pressing force by the control unit 130 will be described later.
  • the suppression of the blood vessel diameter is performed by arbitrarily combining increasing or decreasing the pressing force on the blood vessel.
  • the control unit 130 measures the blood flow rate (volume flow rate) based on the scattered light acquired by the biological sensor 121.
  • the volume flow rate is the volume of fluid (blood) that flows per unit time.
  • the biological sensor 121 includes a light emitting unit 121a and a light receiving unit 121b.
  • the biosensor 121 irradiates the superficial temporal artery with measurement light from the light emitting unit 121a.
  • the biosensor 121 acquires scattered light from the superficial temporal artery with respect to the irradiated measurement light in the light receiving unit 121b.
  • the biological sensor 121 outputs a photoelectric conversion signal of scattered light acquired by the light receiving unit 121b.
  • the biometric sensor 121 transmits a photoelectric conversion signal to the control unit 130.
  • the photoelectric conversion signal transmitted from the biological sensor 121 to the control unit 130 is also referred to as a biological measurement output.
  • the light emitting unit 121 a emits laser light based on the control of the control unit 130.
  • the light emitting unit 121a irradiates a test site with laser light having a wavelength capable of detecting a predetermined component included in blood as measurement light.
  • the light emitting unit 121a is configured by, for example, one LD (Laser Diode: Laser Diode).
  • the light receiving unit 121b receives the scattered light of the measurement light from the test site as biological information.
  • the light receiving unit 121b is configured by, for example, a PD (Photodiode).
  • the control unit 130 calculates the blood flow rate at the test site based on the biometric measurement output received from the biosensor 121.
  • the control unit 130 detects a beat signal (also referred to as a beat signal) generated by light interference between scattered light from a stationary tissue and scattered light from a moving blood cell.
  • the beat signal is a representation of intensity as a function of time.
  • the control unit 130 turns the beat signal into a power spectrum representing power as a function of frequency.
  • FIG. 4 is a diagram illustrating an example of a power spectrum generated by the control unit 130.
  • the horizontal axis represents the Doppler shift frequency f.
  • the vertical axis indicates the power Pw.
  • the Doppler shift frequency f is proportional to the blood cell velocity, and the power Pw corresponds to the amount of blood cells.
  • the blood flow rate Q corresponds to the area of the region indicated by hatching in FIG.
  • the control unit 130 calculates the blood flow rate Q by integrating the power spectrum of the beat signal over the frequency. Specifically, the blood flow is calculated by the following equation (1).
  • the blood flow volume Q calculated by the equation (1) indicates an average blood flow volume.
  • the control unit 130 calculates the average blood pressure of the subject based on the calculated blood flow rate Q.
  • the average blood pressure refers to the average value of blood pressure applied to the artery. It is known that the average blood pressure P is calculated by the following equation (2) using the average blood flow Q and the vascular resistance R.
  • the control unit 130 controls the pressing force adjustment unit 123 so as to suppress a change in the blood vessel diameter (blood vessel radius r). That is, due to a change in the thickness of the pressing force adjusting unit 123, pressure is applied from the measuring apparatus 100 to the blood vessel (superficial temporal artery), and the blood vessel diameter is controlled by this pressure.
  • the control unit 130 may control the pressing force adjustment unit 123 so that the blood vessel diameter becomes a constant value (target value).
  • the control unit 130 may determine the target value of the blood vessel radius r on the basis of the blood flow value calculated based on the first pulse after the start of measurement of biological information, for example.
  • the reference blood vessel radius (that is, the target value) is r 0
  • the blood vessel resistance R when the blood vessel radius r is r 0 is R 0
  • the control unit 130 performs control so that the blood vessel radius r becomes the target value r 0
  • the blood vessel resistance R also becomes the target blood vessel resistance R 0 (constant) according to the Poiseuille's law. Therefore, the average blood pressure P of the subject is proportional to the blood flow rate Q from the above equation (2).
  • the blood flow volume Q calculated based on the first pulse after the start of the measurement of the biological information is set as a reference blood flow volume Q 0, and the average blood pressure P in this case is expressed as the reference average blood pressure P 0 .
  • the reference average blood pressure P 0 is acquired by the control unit 130 as a voltage value indicating the pressure acquired by the pressure sensor 122 at the first pulse or more after the start of measurement of biological information.
  • the control unit 130 determines the target value r 0 based on the value of the first calculated blood flow (reference blood flow Q 0 ) after the start of the measurement of the biological information
  • the target vascular resistance R is obtained from the above equation (2).
  • the control unit 130 can calculate the average blood pressure P of the subject using the following equation (3) by controlling the pressing force adjusting unit 123 so that the vascular resistance R becomes the target vascular resistance R 0 .
  • the control unit 130 can continuously calculate the average blood pressure P using the above equation (3) by continuously calculating the blood flow rate Q.
  • FIG. 5 is a schematic diagram illustrating an example of a blood flow waveform of a subject. As an example, FIG. 5 shows blood flow waveforms for three pulses.
  • the control unit 130 calculates the reference average blood pressure P 0 based on the voltage value indicating the pressure acquired by the pressure sensor 122 with one pulse.
  • the control unit 130 calculates the reference average blood pressure P 0 by dividing the voltage value of the pressure acquired by the pressure sensor 122 during one pulse by the time T required for one pulse.
  • the control unit 130 may calculate the average value of the average blood pressure for the number of pulses and use this as the reference average blood pressure P 0 .
  • the control unit 130 calculates the maximum blood pressure P max and the minimum blood pressure P min using the air cuff 124 and calculates the average blood pressure P based on the following equation (4).
  • the control unit 130 associates the average blood pressure P calculated by the above equation (4) with the average blood flow Q that can be measured within the time taken to calculate the maximum blood pressure P max and the minimum blood pressure P min.
  • a target vascular resistance R 0 is determined according to equation (3).
  • the pressure sensor 122 is calibrated by associating the voltage value indicating the pulse pressure used to calculate the reference average blood pressure P 0 with the pressure value output from the air cuff 124 in the pulse. By calibration, the reference mean blood pressure P 0 expressed as a voltage value can be converted into a pressure value.
  • the reference average blood pressure P 0 is calculated using an oscillometric method for determining blood pressure based on pulse waves, a Korotkoff method for detecting a Korotkoff sound with a microphone, and reading a blood pressure value with a pressure gauge, or tonometry. Laws etc. may be used.
  • control unit 130 can suppress the change in the blood vessel radius r of each pulse by controlling the pressing force adjusting unit 123 so as to suppress the change in the hemoglobin particle amount S of each pulse.
  • the particle amount S of hemoglobin is calculated by the control unit 130 based on the intensity of scattered light received by the light receiving unit 121b of the biological sensor 121, for example.
  • the amount of particles S p of hemoglobin at any point of the pulse beat can be calculated by the following equation (5).
  • the amount of hemoglobin particles for one pulse corresponds to the area of the hatched area in the waveform of each pulse in FIG. 5, for example.
  • the amount of hemoglobin particles S p for one pulse changes according to the blood vessel radius r. Therefore, the control unit 130 controls so as to suppress change in the particle amount S p of hemoglobin at any point of the pulse beat. In this way, the control unit 130 can control the vascular resistance R to be the target vascular resistance R 0 .
  • Control unit 130 instead of the particle amount S p of hemoglobin at any point of the pulse beat, to calculate the average hemoglobin particle amount S pavg the pulse beat, changes in average hemoglobin particle amount S pavg of the pulse beat You may control to suppress. Also by this method, the control unit 130 can control the vascular resistance R to be the target vascular resistance R 0 .
  • the average hemoglobin particle amount S pavg for one pulse can be calculated by the following equation (6).
  • FIG. 6 is a diagram for explaining the calculation of the average amount of hemoglobin particles for one pulse by the measurement device.
  • S p0 is the first sample for the pulse waveform
  • S p1 is the second sample for the pulse waveform
  • S px-1 is the x-1 sample for the pulse waveform
  • S px Indicates the x-th sample for the pulse waveform.
  • X indicates the number of blood flow samples for one pulse.
  • the input unit 140 receives an operation input from the subject.
  • the input unit 140 includes, for example, operation buttons (operation keys).
  • the input unit 140 may be configured by a touch panel, and an operation key that receives an operation input from the subject may be displayed on a part of the display device to accept a touch operation input by the subject.
  • the notification unit 150 notifies information using sound, vibration, images, and the like.
  • the notification unit 150 may include a speaker, a vibrator, and a display device.
  • the display device may be, for example, a liquid crystal display (LCD: Liquid Crystal Display), an organic EL display (OELD: Organic Electro-Luminescence Display), or an inorganic EL display (IELD: Inorganic Electro-Luminescence Display).
  • reports the information regarding the subject's biometric information which the control part 130 measured, for example.
  • the storage unit 160 can be composed of a semiconductor memory or a magnetic memory.
  • the storage unit 160 stores various information and / or programs for operating the measuring apparatus 100 and the like.
  • the storage unit 160 may function as a work memory.
  • the storage unit 160 may store biological information calculated by the control unit 130, for example.
  • the storage unit 160 stores the transition of the average blood pressure P of the subject by storing the average blood pressure P of the subject measured continuously, for example.
  • FIG. 7 is a flowchart in which the measuring apparatus 100 calculates the target vascular resistance R0 .
  • the flowchart shown in FIG. 7 is executed, for example, when the subject wears the measurement apparatus 100 and performs a predetermined operation input for starting measurement processing by the measurement apparatus 100 on the input unit 140.
  • control unit 130 acquires a biological measurement output from the biological sensor 121 (step S101).
  • the control unit 130 calculates the reference blood flow rate Q 0 using, for example, equation (1) based on the biometric measurement output acquired in step S101 (step S102).
  • control unit 130 acquires information about pressure from the pressure sensor 122 as a voltage value (step S103).
  • the control unit 130 calculates a reference average blood pressure P 0 based on the acquired information regarding pressure (step S104).
  • the control unit 130 calculates the target vascular resistance R 0 using, for example, equation (2) (step S105). At this time, the control unit 130 may generate a calculation expression (for example, an expression shown in Expression (3)) for measuring biological information.
  • a calculation expression for example, an expression shown in Expression (3)
  • the control unit 130 stores the target vascular resistance R 0 calculated in step S105 in the storage unit 160 (step S106). Controller 130, when generating a calculation formula with the target vascular resistance R 0 or instead target vascular resistance R 0, may store the generated calculation formula in the storage unit 160.
  • the control unit 130 calculates the particle amount S of hemoglobin based on the biological measurement output acquired in step S101 (step S107).
  • Control unit 130 calculates the particle amount S p of hemoglobin at any point of the pulse beat (step S108).
  • the control unit 130 stores the particle amount S p of hemoglobin at any point of the pulse beat calculated in step S108 in the storage unit 160 (step S109).
  • FIG. 8 is a flowchart in which the measuring apparatus 100 calculates the average blood pressure of the subject as biological information using the target vascular resistance R 0 calculated in FIG.
  • the flowchart shown in FIG. 8 is executed, for example, after the measurement apparatus 100 finishes the flow of FIG.
  • the control unit 130 acquires a biological measurement output from the biological sensor 121 (step S201).
  • the control unit 130 calculates the blood flow rate Q using, for example, the equation (1) based on the biometric measurement output acquired in step S201 (step S202).
  • the control unit 130 calculates the average blood pressure P using the target vascular resistance R0 calculated in step S105 of FIG. 7 (step S203). At this time, the control unit 130 may notify the calculated average blood pressure P from the notification unit 150.
  • the control unit 130 calculates the particle amount S of hemoglobin based on the biological measurement output acquired in step S201 (step S204).
  • Control unit 130 calculates the particle amount S p of hemoglobin at any point of the pulse beat (step S205).
  • the control unit 130 stores the particle amount S p of hemoglobin at any point of the pulse beat calculated in step S205 in the storage unit 160 (step S206).
  • Control unit 130 controls the pressing force adjusting section 123 in accordance with a change in the particle quantity S p of hemoglobin at any point of the pulse beat (step S207).
  • Control unit 130 compares for example the amount of the particles S p of hemoglobin at any point of the pulse beat calculated in step S205, the particle amount S p of hemoglobin at any point one beat before the pulse of the pulse.
  • the pressing force adjusting unit 123 is controlled based on the comparison result.
  • the control unit 130 for example, particle amount S p of hemoglobin at any point of the pulse beat calculated in step S205 is increased than the particle amount S p of hemoglobin at any point one beat before the pulse of the pulse If it is, it is determined that the blood vessel radius tends to expand.
  • control unit 130 controls the pressing force adjusting unit 123 so as to increase the pressing force.
  • the control unit 130 for example, particle amount S p of hemoglobin at any point of the pulse beat calculated in step S205 is reduced than the particle amount S p of hemoglobin at any point one beat before the pulse of the pulse If it is, it is, it is determined that the blood vessel radius tends to decrease.
  • the control unit 130 controls the pressing force adjusting unit 123 so as to weaken the pressing force.
  • control unit 130 can control the pressing force of the pressing force adjusting unit 123 for each pulse.
  • control of the pressing force adjusting unit 123 by the control unit 130 is not limited to each beat.
  • control unit 130 may control the pressing force of the pressing force adjusting unit 123 every predetermined number of beats.
  • the measuring apparatus 100 determines an expansion or contraction tendency of the blood vessel radius based on the biological measurement output output from the biological sensor 121.
  • the measuring apparatus 100 adjusts the pressing force of the pressing force adjusting unit 123 so as to suppress the change in the blood vessel radius based on the determined tendency of the blood vessel radius.
  • the biometric output output from the biometric sensor 121 is also used for calculating biometric information.
  • the measurement apparatus 100 can calculate biological information based on the biological measurement output from the biological sensor 121 and perform control to suppress the change in the blood vessel radius. It can be measured.
  • the measurement apparatus 100 can easily calculate the average blood pressure P as a value proportional to the blood flow volume by performing control to suppress the change in the blood vessel radius.
  • the measuring apparatus 100 acquires a biometric output from the superficial temporal artery. Since the blood vessels of the superficial temporal artery are thicker than blood vessels such as tragus or earlobe, it is easier to acquire more accurate biological information. Therefore, according to the measuring apparatus 100, the measurement accuracy of biological information can be improved.
  • the measuring apparatus 100 performs control for each beat. For this reason, for example, fine control is not required at high speed as the control corresponding to the pulse wave during one pulse is performed.
  • FIG. 9 is a diagram illustrating an example of a mounting state of the measurement apparatus 200 according to the second embodiment of the present disclosure.
  • the measuring apparatus 200 shown in FIG. 9 is used when the subject wears on the ear.
  • the measuring device 200 acquires a biometric output in a state where it is in contact with the test site, and calculates (measures) biometric information from the acquired biometric output.
  • the measuring apparatus 200 acquires a biometric measurement output in the subject's tragus as the test site.
  • the measuring apparatus 200 includes an ear wearing unit 210 and a measuring unit 220 attached to the ear wearing unit 210.
  • the ear mounting unit 210 is a mounting tool for the subject to mount the measuring apparatus 200 on the ear.
  • the measurement unit 220 obtains a biometric output from the test site while in contact with the test site of the subject.
  • FIG. 10 is a cross-sectional view of the measurement unit 220 in the measurement apparatus 200 shown in FIG.
  • FIG. 10 is a cross-sectional view showing a state in which the measurement unit 220 is in contact with the test site.
  • FIG. 10 is a cross-sectional view of the measurement unit 220 viewed from the top of the subject wearing the measurement device 200.
  • the measurement unit 220 includes a clamping unit 230 and a sensor unit 240.
  • the clamping unit 230 is a member for holding the measuring unit 220 between the tragus.
  • the clamping part 230 is formed in a substantially U shape, for example in the cross-sectional view shown in FIG.
  • the clamping part 230 includes a first protrusion 230a and a second protrusion 230b.
  • a sensor part 240 is provided on the first protrusion 230a.
  • the second protrusion 230b is provided with a fixing part 250 for fixing the measuring part 220 to the tragus.
  • the fixed part 250 is configured by a screw (screw) structure, for example.
  • the sensor unit 240 includes a biological sensor 121, a pressure sensor 122, a pressing force adjustment unit 123, and an air cuff 124.
  • the pressing force adjustment unit 123 is an actuator, for example.
  • the biosensor 121 is supported by a biosensor support unit 126, for example.
  • the pressure sensor 122 is supported by the pressure sensor support portion 127.
  • the functions of the biological sensor 121, the pressure sensor 122, the pressing force adjustment unit 123, and the air cuff 124 are the same as those in the first embodiment, and thus detailed description thereof is omitted.
  • the measuring apparatus 200 measures biological information (for example, average blood pressure) by a control unit provided inside (for example, the ear wearing unit 210). Since the measurement process of the biological information by the measurement apparatus 200 is the same as that of the first embodiment, detailed description thereof is omitted here.
  • the measuring device 200 may include a communication unit for performing wired or wireless communication with a terminal device, for example.
  • the terminal device may include a control unit that executes a part of the biological information measurement function, for example.
  • the measuring apparatus 200 can measure biological information with a simpler structure, like the measuring apparatus 100 according to the first embodiment.
  • the pressing force adjusting unit 123 that adjusts the pressing force to the test site is a cuff
  • a sound is generated when air is taken in and out of the cuff. Therefore, since the subject feels stress or feels bothersome, it is difficult to always measure biological information.
  • the pressing force adjusting unit 123 is an actuator (conductive polymer actuator)
  • no sound is generated due to the above-described air flow when adjusting the pressing force, or if the sound is slightly Even if it occurs, it is difficult to convey to the subject. Therefore, the subject is less likely to feel stress, and the biological information can be constantly measured by wearing the measuring device 200 at all times.
  • test site is a temple and a tragus
  • test site is not limited thereto.
  • the test site may be any site that can acquire a biometric output from the biosensor 121.

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

Abstract

Ce dispositif de mesure est pourvu : d'une unité de sortie qui délivre un signal sur la base d'une lumière diffusée provenant d'un site d'examen; d'une unité de réglage de force de pression pour ajuster une force de pression par rapport au site d'examen; et d'une unité de commande qui, sur la base du signal, contrôle la force de pression par rapport au site d'examen, résultant de l'unité de réglage de force de pression.
PCT/JP2017/036396 2016-10-05 2017-10-05 Dispositif de mesure, méthode de mesure et programme WO2018066680A1 (fr)

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1993004625A1 (fr) * 1991-08-30 1993-03-18 Baxter International Inc. Ensemble capteur de la pression du sang de l'artere temporale sans introduction dans le corps
US5617868A (en) * 1994-11-22 1997-04-08 Colin Corporation Pulse wave detecting apparatus
JP2007330638A (ja) * 2006-06-16 2007-12-27 Sharp Corp 生体信号測定装置
JP2008114037A (ja) * 2006-10-12 2008-05-22 Nippon Telegr & Teleph Corp <Ntt> 血圧測定装置及び血圧測定装置制御方法
JP2016158849A (ja) * 2015-02-28 2016-09-05 シナノケンシ株式会社 疾病発症危険度変化早期警報システム

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1993004625A1 (fr) * 1991-08-30 1993-03-18 Baxter International Inc. Ensemble capteur de la pression du sang de l'artere temporale sans introduction dans le corps
US5617868A (en) * 1994-11-22 1997-04-08 Colin Corporation Pulse wave detecting apparatus
JP2007330638A (ja) * 2006-06-16 2007-12-27 Sharp Corp 生体信号測定装置
JP2008114037A (ja) * 2006-10-12 2008-05-22 Nippon Telegr & Teleph Corp <Ntt> 血圧測定装置及び血圧測定装置制御方法
JP2016158849A (ja) * 2015-02-28 2016-09-05 シナノケンシ株式会社 疾病発症危険度変化早期警報システム

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