US20040186387A1 - Pulse meter, method for controlling pulse meter, wristwatch-type information device, control program, storage medium, blood vessel simulation sensor, and living organism information measurement device - Google Patents

Pulse meter, method for controlling pulse meter, wristwatch-type information device, control program, storage medium, blood vessel simulation sensor, and living organism information measurement device Download PDF

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Publication number
US20040186387A1
US20040186387A1 US10/793,419 US79341904A US2004186387A1 US 20040186387 A1 US20040186387 A1 US 20040186387A1 US 79341904 A US79341904 A US 79341904A US 2004186387 A1 US2004186387 A1 US 2004186387A1
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Prior art keywords
pulse wave
body motion
pulse
sensor
detection signal
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US10/793,419
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English (en)
Inventor
Tsukasa Kosuda
Makoto Zakoji
Ichiro Aoshima
Yutaka Kawafune
Norimitsu Baba
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Seiko Epson Corp
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Seiko Epson Corp
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Assigned to SEIKO EPSON CORPORATION reassignment SEIKO EPSON CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ZAKOJI, MAKOTO, AOSHIMA, ICHIRO, BABA, NORIMITSU, KAWAFUNE, YUTAKA, KOSUDA, TSUKASA
Publication of US20040186387A1 publication Critical patent/US20040186387A1/en
Priority to US12/203,599 priority Critical patent/US8303512B2/en
Abandoned legal-status Critical Current

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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
    • A61B5/68—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
    • A61B5/02—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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • 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
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
    • A61B5/721—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts using a separate sensor to detect motion or using motion information derived from signals other than the physiological signal to be measured
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0219—Inertial sensors, e.g. accelerometers, gyroscopes, tilt switches
    • 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
    • A61B5/7235—Details of waveform analysis
    • A61B5/7253—Details of waveform analysis characterised by using transforms
    • A61B5/7257—Details of waveform analysis characterised by using transforms using Fourier transforms

Definitions

  • the present invention relates to a pulse meter, a method for controlling a pulse meter, a wristwatch-type information device, a control program, a storage medium, a blood vessel simulation sensor, and a living organism information measurement device.
  • the present invention particularly relates to a pulse meter, a method for controlling a pulse meter, a wristwatch-type information device, a control program, a storage medium, a blood vessel simulation sensor, and a living organism information measurement device that are suitable for being mounted on a person's arm and measuring pulse during walking or running.
  • Pulse meters mounted on part of the body and designed for measuring pulse during walking or running are conventionally known.
  • a wristwatch-type pulse meter is disclosed in Japanese Patent No. 2816944.
  • the pulse meter disclosed in this literature employs a configuration wherein the frequency components corresponding to all the harmonic components of a body motion signal detected by an acceleration sensor are removed from the frequency analysis results of a pulse wave signal based on the frequency analysis results of the body motion signal, the frequency components having the maximum power are extracted from among the frequency analysis results of the pulse wave signal from which the harmonic components of the body motion signal have been removed, and the pulse rate is calculated based on the extracted frequency components.
  • the body motion components cannot be registered completely, so the body motion signal is identified using the characteristics of the harmonic components from the frequency analysis results in order to remove the body motion components contained in the pulse sensor signal, and because the identified body motion signal is removed and the pulse wave signal extracted, there have been problems in that the body motion components cannot be removed and, consequently, the pulse cannot be correctly determined when the body motion does not have cyclic characteristics.
  • An object of the present invention is to provide a pulse meter, a method for controlling a pulse meter, a wristwatch-type information device, a control program, a storage medium, a blood vessel simulation sensor, and a living organism information measurement device that can accurately remove the body motion components generated in the body from the pulse components and calculate the pulse rate even when the body motion components do not have cyclic characteristics by more accurately registering the body motion components contained in the pulse sensor signal.
  • a living organism information measurement device adapted to be attached to a human body to measure living organism information
  • the pulse wave detecting section is configured and arranged to output a pulse wave detection signal by using a pulse wave sensor.
  • the body motion component removing section is configured and arranged to detect a body motion component resulting from vein movements of the human body that is contained in the pulse wave detection signal and remove said body motion component contained in the pulse wave detection signal.
  • the living organism information measuring section is configured and arranged to measure living organism information based on the pulse wave detection signal from which the body motion component has been removed.
  • a pulse meter adapted to be attached to a human body to measure a pulse of the human body
  • the pulse wave detecting section is configured and arranged to detect a pulse wave based on a signal from a pulse wave sensor and output a pulse wave detection signal.
  • the body motion detecting section is configured and arranged to detect accelerations corresponding to body motions that affect a vein behavior based on a signal from an acceleration sensor and output a body motion detection signal.
  • the body motion component removing section is configured and arranged to remove a body motion component contained in the pulse wave detection signal based on the body motion detection signal.
  • the pulse rate calculating section is configured and arranged to calculate a pulse rate based on the pulse wave detection signal from which the body motion component has been removed.
  • a pulse meter adapted to be attached to a human body to measure a pulse
  • the pulse wave detecting section is configured and arranged to detect a pulse wave based on a signal from a pulse wave sensor and output a pulse wave detection signal.
  • the body motion component removing section is configured and arranged to remove a body motion component contained in the pulse wave detection signal based on a relative positional difference in a vertical direction between a position of a heart of the human body and a position where the pulse meter is attached.
  • the pulse rate calculating section is configured and arranged to calculate a pulse rate based on the pulse wave detection signal from which the body motion component has been removed.
  • a blood vessel simulation sensor adapted to be attached to a human body to simulate a behavior of blood in vein of the human body
  • the simulation blood is disposed inside the casing and has a viscosity substantially equal to a viscosity of the blood in vein.
  • the behavior detection sensor is configured and arranged to detect a behavior of the simulation blood.
  • FIG. 1 is an explanatory diagram of the relationship between the amount of change in a combined vector of acceleration vectors along two axes and the amount of body motion components (amount of stroke components) included in the output of a pulse sensor;
  • FIG. 2 is an explanatory diagram of the manner in which the pulse measurement device of a first embodiment is mounted
  • FIG. 3 is a cross-sectional view of the pulse measurement device of the first embodiment
  • FIG. 4 is a schematic structural block diagram of the pulse measurement device of the first embodiment
  • FIG. 5 is a schematic structural block diagram of an example of an adaptive filter of the first embodiment
  • FIG. 6 is a graph showing a chronological arrangement of X-axis acceleration data Kx corresponding to an X-axis acceleration detection signal outputted from an X-axis acceleration sensor 12 X;
  • FIG. 7 shows the frequency analysis results obtained by subjecting the detected X-axis acceleration data Kx in FIG. 6 to FFT;
  • FIG. 8 is a graph showing a chronological arrangement of Y-axis acceleration data Ky corresponding to a Y-axis acceleration detection signal outputted from a Y-axis acceleration sensor 12 Y;
  • FIG. 9 shows the frequency analysis results obtained by subjecting the detected Y-axis acceleration data Ky in FIG. 8 to FFT;
  • FIG. 10 is a graph showing a chronological arrangement of Z-axis acceleration data Kz corresponding to a Z-axis acceleration detection signal outputted from a Z-axis acceleration sensor 12 Z;
  • FIG. 11 shows the frequency analysis results obtained by subjecting the detected Z-axis acceleration data Kz in FIG. 10 to FFT;
  • FIG. 12 is a graph obtained by treating the Y-axis acceleration data Ky corresponding to the Y-axis acceleration detection signal outputted from the Y-axis acceleration sensor 12 Y, and the Z-axis acceleration data Kz corresponding to the Z-axis acceleration detection signal outputted from the Z-axis acceleration sensor 12 Z as vectors, and chronologically arranging combined acceleration vector data obtained as a combined vector thereof;
  • FIG. 14 is a graph showing a chronological arrangement of a preset simulated low-frequency signal (using a triangular wave);
  • FIG. 15 shows the frequency analysis results obtained by subjecting the simulated low-frequency signal in FIG. 14 to FFT;
  • FIG. 16 is a graph of a chronological arrangement of one example of the detected pulse data
  • FIG. 17 shows the frequency analysis results obtained by subjecting the detected pulse data in FIG. 16 to FFT
  • FIG. 18 is a graph plotted as a result of a chronological arrangement of residual data obtained by combining the signals obtained by applying an adaptive filter to the amplified X-axis acceleration detection signal in FIG. 6, the combined acceleration vector signal in FIG. 12, and the simulated low-frequency signal in FIG. 14 for the pulse wave detection signal in FIG. 16;
  • FIG. 19 shows the frequency analysis results obtained by subjecting the residual data in FIG. 18 to FFT
  • FIG. 20 is a graph plotted as a result of a chronological arrangement of residual data obtained by combining the signals obtained by applying an adaptive filter to the amplified X-axis acceleration detection signal in FIG. 6 and the combined acceleration vector signal in FIG. 12 for the pulse wave detection signal in FIG. 16;
  • FIG. 21 shows the frequency analysis results obtained by subjecting the residual data in FIG. 20 to FFT
  • FIG. 22 is a schematic structural block diagram of one example of an adaptive filter according to a first alternative of the first embodiment
  • FIG. 23 is a graph of a chronological arrangement of detected X-axis acceleration data Kx;
  • FIG. 24 shows the frequency analysis results obtained by subjecting the detected X-axis acceleration data Kx in FIG. 23 to FFT;
  • FIG. 25 is a graph of a chronological arrangement of Y-axis acceleration data Ky
  • FIG. 26 shows the frequency analysis results obtained by subjecting the Y-axis acceleration data Ky in FIG. 25 to FFT;
  • FIG. 27 is a graph of a chronological arrangement of Z-axis acceleration data Kz
  • FIG. 28 shows the frequency analysis results obtained by subjecting the Z-axis acceleration data Kz in FIG. 27 to FFT;
  • FIG. 31 is a graph of a chronological arrangement of one example of detected pulse wave data
  • FIG. 32 shows the frequency analysis results obtained by subjecting the detected pulse wave data in FIG. 31 to FFT
  • FIG. 33 is a graph of a chronological arrangement of residual data obtained by combining the data obtained by applying an adaptive filter to the combined acceleration vector data in FIG. 29 and the simulated low-frequency signal in FIG. 14 for the deteceted pulse wave data in FIG. 31;
  • FIG. 34 shows the frequency analysis results obtained by subjecting the residual data in FIG. 33 to FFT
  • FIG. 35 is a schematic structural block diagram of one example of an adaptive filter according to a second alternative of the first embodiment
  • FIG. 36 is a graph of a chronological arrangement of one example of detected pulse wave data
  • FIG. 37 shows the frequency analysis results obtained by subjecting the detected pulse wave data in FIG. 36 to FFT
  • FIG. 38 is a graph of a chronological arrangement of residual data obtained by combining the signals obtained by applying an adaptive filter to the combined acceleration vector signal in FIG. 29 and the simulated low-frequency signal in FIG. 14 for the detected pulse wave data in FIG. 31;
  • FIG. 39 shows the frequency analysis results obtained by subjecting the residual data in FIG. 38 to FFT
  • FIG. 40 is a schematic structural block diagram of one example of an adaptive filter according to a third alternative of the first embodiment
  • FIG. 41 is a schematic structural block diagram of one example of an adaptive filter according to a fourth alternative of the first embodiment
  • FIG. 42 is an explanatory diagram of the relationship between the amount of change in pressure and the amount of body motion components (amount of stroke components) included in the pulse wave sensor output;
  • FIG. 43 is a schematic structural diagram of a pulse measurement device of the second embodiment
  • FIG. 44 is an explanatory diagram of the arrangement of sensors in the sensor module of the pulse measurement device of the second embodiment
  • FIG. 45 is a schematic structural block diagram of the pulse measurement device of the second embodiment.
  • FIG. 46 is a graph of a chronological arrangement of one example of detected pulse wave data
  • FIG. 47 is a graph in which detected pressure data correlated with the detected pulse wave data in FIG. 46 is chronologically arranged along the same time axis;
  • FIG. 48 is a graph of a chronological arrangement of differential data calculated from the detected pulse wave data in FIG. 46 and the detected pressure data in FIG. 6;
  • FIG. 49 shows the frequency analysis results obtained by subjecting the differential data in FIG. 48 to FFT
  • FIG. 50 is an explanatory diagram of the frequency analysis results of the detected pulse wave data according to a first alternative of the second embodiment
  • FIG. 51 is an explanatory diagram of the frequency analysis results of the detected pressure data according to the first alternative of the second embodiment
  • FIG. 52 is an explanatory diagram of differential data, which is the difference between the detected pulse wave data analyzed for frequency and the detected pressure data analyzed for frequency, according to the first alternative of the second embodiment;
  • FIG. 53 shows a schematic structural block diagram of one example of the adaptive filter in accordance with a second alternative of the second embodiment
  • FIG. 54 is a graph of a chronological arrangement of an example of the detected pulse wave data according to the second alternative of the second embodiment
  • FIG. 55 is a graph in which detected pressure data correlated with the detected pulse wave data in FIG. 54 is chronologically arranged along the same time axis;
  • FIG. 56 is a graph of a chronological arrangement of residual data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 54 and the detected pressure data in FIG. 55;
  • FIG. 57 shows the frequency analysis results obtained by subjecting the residual data in FIG. 56 to FFT
  • FIG. 58 is a schematic structural block diagram of a pulse measurement device according to a third alternative of the second embodiment.
  • FIG. 59 is an explanatory diagram of the arrangement of sensors in a sensor module 111 A of the third alternative of the second embodiment
  • FIG. 60 is an explanatory diagram of the arrangement of the sensors in a sensor module 111 B of the third alternative of the second embodiment
  • FIG. 61 is an explanatory diagram of the relationship between the amount of change in height of the arm and the amount of body motion components (amount of stroke components) included in the pulse wave sensor output;
  • FIG. 62 is an explanatory diagram of the relationship between the angle and direction of the arm
  • FIG. 63 is an explanatory diagram of the relationship between the amount of change in height of the arm position in the arm position (direction of the arm) in its initial state and the amount of body motion components (stroke components) as an angle sensor output;
  • FIG. 64 is an explanatory diagram of the change in the amount of body motion components (stroke components) as the angle sensor output depending on the position of the arm when the amount of change in height is fixed;
  • FIG. 65 is an explanatory diagram of the relationship between the amount of change in height of the arm position in the position of the arm (direction of the arm) in its initial state and the amount of body motion components (stroke components) included in the angle sensor output after correction;
  • FIG. 66A is a cross-sectional view of a pulse measurement device of a third embodiment which is incorporated into a watchcase;
  • FIG. 66B is a schematic structural block diagram of the pulse measurement device of the third embodiment.
  • FIG. 66C shows a schematic structural block diagram of one example of an adaptive filter of the third embodiment
  • FIG. 67 is a schematic structural diagram of a differential capacitive sensor, which is an angle sensor
  • FIG. 68 is a partial enlarged diagram of the differential capacitive sensor
  • FIG. 69 is an explanatory diagram of the operation of the differential capacitive sensor
  • FIG. 70 is a front view of a rotary-spindle angle sensor used as an angle sensor
  • FIG. 71 is a side view of the rotary-spindle angle sensor in FIG. 70;
  • FIG. 72 is a graph of a chronological arrangement of one example of detected pulse wave data
  • FIG. 73 shows the frequency analysis results obtained by subjecting the detected pulse wave data in FIG. 72 to FFT;
  • FIG. 74 is a graph of a chronological arrangement of one example of detected angle data
  • FIG. 75 shows the frequency analysis results obtained by subjecting the detected angle data in FIG. 74 to FFT
  • FIG. 76 is a graph of a chronological arrangement of residual data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 72 and the detected angle data in FIG. 74;
  • FIG. 77 shows the frequency analysis obtained by subjecting the residual data in FIG. 76 to FFT
  • FIG. 78 is a graph of a chronological arrangement of one example of corrected detected angle data
  • FIG. 79 shows the frequency analysis obtained by subjecting the corrected detected angle data to FFT
  • FIG. 80 is a graph of a chronological arrangement of residual data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 72 and the corrected detected angle data in FIG. 78;
  • FIG. 81 shows the frequency analysis results obtained by subjecting the residual data in FIG. 80 to FFT
  • FIG. 82 is a diagram illustrating the principle of a blood vessel simulation sensor mounted on the body and designed for simulating the movement (behavior) of venous blood;
  • FIG. 83 is a schematic diagram of a first rigid type of blood vessel simulation sensor
  • FIG. 84 is a schematic diagram of a second rigid type of blood vessel simulation sensor
  • FIG. 85 is a schematic diagram of a first elastic type of blood vessel simulation sensor
  • FIG. 86 is a schematic diagram of a second elastic type of blood vessel simulation sensor
  • FIG. 87 is an explanatory diagram of the relationship between a rigid type of blood vessel simulation sensor and the body motion components (stroke components) included in the pulse wave sensor output;
  • FIG. 88 is an explanatory diagram of the relationship between an elastic type of blood vessel simulation sensor and the body motion components (stroke components) included in the pulse sensor output;
  • FIG. 89 is a schematic structural block diagram of a pulse measurement device of the fourth embodiment.
  • FIG. 90 is an explanatory diagram of the arrangement of the sensors in a sensor module of the pulse measurement device of the fourth embodiment in a mounted state;
  • FIG. 91 is a schematic structural block diagram of the pulse measurement device of the fourth embodiment.
  • FIG. 92 is a graph of a chronological arrangement of one example of the detected pulse wave data according to the fourth embodiment.
  • FIG. 93 is a graph in which detected pressure data correlated with the detected pulse wave data in FIG. 92 is chronologically arranged along the same time axis;
  • FIG. 94 is a graph of a chronological arrangement of differential data calculated from the detected pulse wave data in FIG. 92 and the detected pressure data in FIG. 93;
  • FIG. 95 shows the frequency analysis results obtained by subjecting the differential data in FIG. 94 to FFT
  • FIG. 96 is an explanatory diagram of the frequency analysis results of the detected pulse wave data in a first alternative of the fourth embodiment
  • FIG. 97 is an explanatory diagram of the frequency analysis results of detected pressure data
  • FIG. 98 is an explanatory diagram of differential data, which is the difference between detected pulse wave data after analyzed for frequency and detected pressure data after analyzed for frequency;
  • FIG. 99 is a schematic structural block diagram of one example of an adaptive filter in a second alternative of the fourth embodiment.
  • FIG. 100 is a graph of a chronological arrangement of one example of the detected pulse wave data in the second alternative of the fourth embodiment
  • FIG. 101 is a graph in which pressure detection data correlated with the detected pulse wave data in FIG. 100 is chronologically arranged along the same time axis;
  • FIG. 102 is a graph of a chronological arrangement of differential data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 100 and the detected pressure data in FIG. 20;
  • FIG. 103 shows the frequency analysis results obtained by subjecting the differential data in FIG. 102 to FFT
  • FIG. 104A is an explanatory diagram of the arrangement of sensors in a sensor module of a mounted pulse measurement device according to a third alternative of the fourth embodiment, in a mounted state;
  • FIG. 104B is a schematic structural block diagram of the pulse measurement device according to the third alternative of the fourth embodiment.
  • FIG. 105A is an explanatory diagram of the arrangement of sensors in a sensor module of a pulse measurement device according to a fourth alternative of the fourth embodiment, in a mounted state;
  • FIG. 105B is a schematic structural block diagram of the pulse measurement device according to the fourth alternative of the fourth embodiment.
  • FIG. 106 is an explanatory diagram of the relationship between acceleration in the direction of the X-axis described hereinbelow, when a triaxial (X, Y, Z-axes) acceleration sensor is used as an acceleration sensor, and the body motion components (stroke components) included in the pulse wave sensor output signal;
  • FIG. 107 is an explanatory diagram of the relationship between acceleration in the direction of the Y-axis described hereinbelow, when a triaxial acceleration sensor described hereinbelow is used as an acceleration sensor, and the body motion components (stroke components) included in the pulse wave sensor output signal;
  • FIG. 108 is an explanatory diagram of the relationship between acceleration in the direction of the Z-axis, when a triaxial (X, Y, Z-axes) acceleration sensor described hereinbelow is used as an acceleration sensor, and the body motion components (stroke components) included in the pulse wave sensor output signal;
  • FIG. 109 is an explanatory diagram of the three axes
  • FIG. 110 is an external perspective view of a pulse measurement device of a fifth embodiment
  • FIG. 111 is a cross-sectional view of the sensor module in FIG. 110;
  • FIG. 112 is an external perspective view of a case in which a pulse measurement device of a sixth embodiment is incorporated in a watchcase.
  • FIG. 113 is a cross-sectional view of the pulse measurement device in FIG. 112.
  • a pulse measurement device 10 will be described herein according to a first embodiment of the present invention. First, the operational basis for the first embodiment will be described prior to a detailed description of the first embodiment.
  • the output from a pulse wave sensor for detecting pulse waves includes various body motion components in addition to pulse wave components. It is known that these body motion components are generated by the changes in the body, particularly by the behavior of venous blood, originating in the movement of the user (walking/running, arm movement, and the like) whose pulse is to be measured.
  • FIG. 1 is an explanatory diagram of the relationship between the amount of change in a combined vector of acceleration vectors along two axes and the amount of body motion components (amount of stroke components) included in the output of a pulse sensor.
  • the amount of change in the combined vector of the two axial acceleration vectors and the amount of body motion components (amount of stroke components) included in the output of the pulse sensor have a substantially proportional relationship.
  • the body motion components originating in the veins are detected by a triaxial acceleration sensor, and the pulse rate is accurately detected based on a signal that is free of the effect of venous blood by subtracting the detected output from the output of the pulse wave sensor in a specific proportion.
  • FIG. 2 is an explanatory diagram of the manner in which the pulse meter or pulse measurement device 10 of the first embodiment is mounted.
  • the pulse measurement device 10 is used while mounted on the user's arm 11 , and has a device main body (watchcase) 10 A and a wristband 10 B for mounting the device main body 10 A on the arm.
  • the pulse measurement device 10 according to the present embodiment functions as a living organism information measurement device mounted on the body and designed for measuring living organism information, or as a wristwatch-type information device mounted on the arm.
  • FIG. 3 is a cross-sectional view of the pulse measurement device of the first embodiment.
  • the back surface of the device main body 10 A is pressed against the back of the wrist when the pulse measurement device 10 is mounted with the wristband 10 B wound around the wrist.
  • the reverse side of the device main body 10 A is provided with a triaxial (X-axis, Y-axis, Z-axis) acceleration sensor 12 and a pulse wave sensor 13 .
  • the triaxial acceleration sensor 12 functions as a body motion sensor.
  • the pulse wave sensor 13 has an LED 13 A for emitting light to detect pulse waves, a PD (Photo Detector) 13 B for receiving the detection light reflected by the body, and transparent glass 13 C for protecting the LED 13 A and the PD 13 B, transmitting the light incident on the LED 13 A and reflected light obtained via the body, and directing the light onto the PD 13 B.
  • the transparent glass 13 C is fixed by means of a back lid 14 as a component of the device main body 10 A.
  • the configuration of this pulse wave sensor 13 is designed such that light from the LED 13 A is reflected from the back of the wrist through the transparent glass 13 C, and the reflected light is received by the photo detector 13 B.
  • the front side of the device main body 10 A is provided with a liquid crystal display device 15 for displaying the pulse rate HR and other such living organism information based on the detection results from the pulse wave sensor 13 in addition to the current time and date. Also, the interior of the device main body 10 A has a CPU and other such IC circuits on a main board 16 , whereby a data processing circuit 17 is configured.
  • the reverse side of the main board 16 is provided with a battery 18 , which supplies power to the triaxial acceleration sensor, the pulse wave sensor 13 , the liquid crystal display device 15 , and the main board 16 .
  • the triaxial acceleration sensor 12 and the pulse wave sensor 13 are connected with the main board 16 by a heat seal 19 . Power is supplied from the main board 16 to the triaxial acceleration sensor 12 and the pulse wave sensor 13 through a wiring formed by the heat seal 19 . As a result, an acceleration detection signal is fed from the triaxial acceleration sensor 12 to the main board 16 . Also, a pulse wave detection signal is fed from the pulse wave sensor 13 to the main board 16 .
  • the data processing circuit 17 subjects the acceleration detection signal and the pulse wave detection signal to FFT processing, and the pulse rate HR is calculated by analyzing the processing results.
  • the external surface of the device main body 10 A is provided with a plurality of button switches 20 A, 20 B, 20 C, 20 D, and 20 E for time setting, display mode switching, and the like, as shown in FIG. 1.
  • FIG. 4 is a schematic structural block diagram of the pulse measurement device 10 of the first embodiment.
  • the pulse measurement device 10 has a pulse wave signal amplifying circuit 21 , an acceleration signal amplifying circuit 22 , an A/D conversion circuit 23 , and an MPU 24 , a RAM 25 , and a ROM 26 in addition to the triaxial acceleration sensor 12 , the pulse wave sensor 13 , and the liquid crystal display device 15 described above.
  • the pulse wave sensor 13 , the pulse wave signal amplifying circuit 21 , and the A/D conversion circuit 23 together constitute a pulse wave detecting section.
  • the triaxial acceleration sensor 12 , the acceleration signal amplifying circuit 22 , and the A/D conversion circuit 23 together constitute a body motion detecting section.
  • the triaxial acceleration sensor 12 has an X-axis acceleration sensor 12 X for detecting acceleration in the direction of the X-axis, a Y-axis acceleration sensor 12 Y for detecting acceleration in the direction of the Y-axis, and a Z-axis acceleration sensor 12 Z for detecting acceleration in the direction of the Z-axis shown in FIG. 1 or 2 .
  • the pulse wave signal amplifying circuit 21 amplifies the pulse wave detection signal outputted from the pulse wave sensor 13 at a prescribed rate of amplification, and outputs the result to the A/D conversion circuit 23 as an amplified pulse wave detection signal.
  • the acceleration signal amplifying circuit 22 amplifies the X-axis acceleration detection signal, the Y-axis acceleration detection signal, and the Z-axis acceleration detection signal outputted from the triaxial acceleration sensor 12 at a prescribed rate of amplification, and outputs the result to the A/D conversion circuit 23 as an amplified X-axis acceleration detection signal, an amplified Y-axis acceleration detection signal, and an amplified Z-axis acceleration detection signal.
  • the A/D conversion circuit 23 performs analog/digital conversion separately on the inputted amplified pulse wave detection signal, the amplified X-axis acceleration detection signal, the amplified Y-axis acceleration detection signal, the amplified Z-axis acceleration detection signal, and the amplified pressure detection signal, and outputs the result to the MPU 24 as detected pulse wave data or pulse wave detection data, detected X-axis acceleration data Kx, Y-axis acceleration data Ky, and Z-axis acceleration data Kz.
  • the MPU 24 stores the detected X-axis acceleration data Kx, the detected Y-axis acceleration data Ky, and the detected Z-axis acceleration data Kz in the RAM 25 , calculates the pulse rate based on a control program stored in the ROM 26 , and displays the result on the display device 15 .
  • the MPU 24 chronologically arranges the detected pulse wave data stored in the RAM 25 as well as detected body motion data or body motion detection data obtained based on the detected X-axis acceleration data Kx, the detected Y-axis acceleration data Ky, and the detected Z-axis acceleration data Kz, and determines residual data, which is the difference between the detected pulse wave data and the detected body motion data for each sampling time.
  • Frequency analysis FFT: Fast Fourier Transformation
  • the MPU 24 also essentially functions as a body motion component generating section.
  • FIG. 5 is a schematic structural block diagram of one example of an adaptive filter 30 of the first embodiment.
  • the adaptive filter 30 has a filter coefficient generating section 31 and a synthesizer 32 .
  • a coefficient controller 31 A of the filter coefficient generating section 31 functions as a body motion component removing section and generates an adaptive filter coefficient h based on previously outputted data by the synthesizer 32 to which the filter has been applied.
  • these effects were removed by applying an adaptive filter upon multiplying the output signal from the triaxial acceleration sensor 12 , which is the body motion detection sensor, by a simulated low-frequency signal whose frequency corresponds to a low-frequency variation component.
  • the simulated low-frequency signal must have a specific frequency distribution during frequency analysis and remove low-frequency variation components, and should be a triangular or rectangular wave of 0.5 Hz or less in view of the fact that the frequency band thereof is 0.5 Hz or less.
  • the frequency band and the waveform can be appropriately varied in accordance with the actually contained low-frequency variation components.
  • FIG. 6 is a graph showing a chronological arrangement of X-axis acceleration data Kx for the X-axis acceleration detection signal outputted from the X-axis acceleration sensor 12 X.
  • FIG. 7 shows the frequency analysis results obtained by subjecting the detected X-axis acceleration data Kx in FIG. 6 to FFT.
  • FIG. 8 is a graph showing a chronological arrangement of Y-axis acceleration data Ky for the Y-axis acceleration detection signal outputted from the Y-axis acceleration sensor 12 Y.
  • FIG. 9 shows the frequency analysis results obtained by subjecting the detected Y-axis acceleration data Ky in FIG. 8 to FFT.
  • FIG. 10 is a graph showing a chronological arrangement of Z-axis acceleration data Kz for the Z-axis acceleration detection signal outputted from the Z-axis acceleration sensor 12 Z.
  • FIG. 11 shows the frequency analysis results obtained by subjecting the detected Z-axis acceleration data Kz in FIG. 10 to FFT.
  • FIG. 12 is a graph obtained by treating the Y-axis acceleration data Ky corresponding to the Y-axis acceleration detection signal outputted from the Y-axis acceleration sensor 12 Y, and the Z-axis acceleration data Kz corresponding to the Z-axis acceleration detection signal outputted from the Z-axis acceleration sensor 12 Z as vectors, and chronologically arranging combined acceleration vector data obtained as a combined vector thereof.
  • FIG. 14 is a graph showing a chronological arrangement of a preset simulated low-frequency signal (using a triangular wave).
  • FIG. 15 shows the frequency analysis results obtained by subjecting the simulated low-frequency signal in FIG. 14 to FFT. As can be seen from FIG. 15, the frequency is approximately 0.5 Hz or less, with a specific frequency distribution.
  • FIG. 16 is a graph of a chronological arrangement of one example of the detected pulse data.
  • FIG. 17 shows the frequency analysis results obtained by subjecting the detected pulse data in FIG. 16 to FFT.
  • the MPU 24 sequentially reads the detected pulse wave data, the detected X-axis acceleration data, the detected Y-axis acceleration data, and the detected Z-axis acceleration data stored in the RAM 25 , and outputs the detected pulse wave data in a single sampling period to the synthesizer 32 .
  • the MPU 24 outputs the detected X-axis acceleration data Kx, the detected Y-axis acceleration data Ky, and the detected Z-axis acceleration data Kz corresponding to the detected pulse wave data outputted to the synthesizer 32 to the filter coefficient generating section 31 .
  • the synthesizer 32 combines the current pulse wave data and the body motion removal data h(x), h(y), and h(z); substantially removes (subtracts) the body motion components contained in the current detected pulse wave data; extracts the pulse wave components; and outputs the residual data e(n), which is the data to which the adaptive filter has been applied.
  • FIG. 18 is a graph plotted as a result of a chronological arrangement of the residual data obtained by combining the signals obtained by applying an adaptive filter to the amplified X-axis acceleration detection signal in FIG. 6, the combined acceleration vector signal in FIG. 12, and the simulated low-frequency signal in FIG. 14 for the pulse wave detection signal in FIG. 16.
  • FIG. 19 shows the frequency analysis results obtained by subjecting the residual data in FIG. 18 to FFT.
  • the frequency analysis results thus obtained have the body motion components originating in the veins substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor, and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • FIG. 20 is a graph of a chronological arrangement of residual data obtained by combining the signals obtained by applying an adaptive filter to the amplified X-axis acceleration detection signal in FIG. 6 and the combined acceleration vector signal in FIG. 12 for the pulse wave detection signal in FIG. 16.
  • FIG. 21 shows the frequency analysis results obtained by subjecting the residual data in FIG. 20 to FFT.
  • the MPU 24 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data primarily containing pulse wave components constitute the pulse spectrum. Therefore, the MPU 24 functions as a pulse rate calculating section. The MPU 24 then displays the pulse rate on the liquid crystal display device 15 .
  • the MPU 24 can also be configured so as to calculate the pitch or the number of steps of the user from the detected body motion components.
  • the MPU 24 functions as a body motion information detecting section for detecting the pitch or the number of steps.
  • variation in the veins which is the main factor in the body motion components generated in the body, can be surely detected and registered by using the pulse wave sensor 13 and the triaxial acceleration sensor 12 functioning as a body motion sensor, and also by using a simulated low-frequency signal. Therefore, the body motion components can be surely removed, making it possible to accurately detect pulse wave components, and hence to accurately measure the pulse rate.
  • FIG. 22 is a schematic structural block diagram of one example of the adaptive filter 40 of the first alternative of the first embodiment.
  • the adaptive filter 40 has a filter coefficient generating section 41 , an integrator 42 , and a synthesizer 43 .
  • the filter coefficient generating section 41 functions as a body motion component removing section, and generates an adaptive filter coefficient h based on data previously outputted by the synthesizer 43 after the filter has been applied.
  • the filter coefficient generating section 41 applies the generated adaptive filter coefficient h to the output from the integrator 42 , generates body motion removal data h(Kx 2 +Ky 2 +Kz 2 ), and outputs the result to the synthesizer 43 .
  • FIG. 23 is a graph of a chronological arrangement of detected X-axis acceleration data Kx for the X-axis acceleration detection signal outputted from the X-axis acceleration sensor 12 X.
  • FIG. 24 shows the frequency analysis results obtained by subjecting the detected X-axis acceleration data Kx in FIG. 23 to FFT.
  • FIG. 25 is a graph of a chronological arrangement of Y-axis acceleration data Ky for the Y-axis acceleration detection signal outputted from the Y-axis acceleration sensor 12 Y.
  • FIG. 26 shows the frequency analysis results obtained by subjecting the detected Y-axis acceleration data Ky in FIG. 25 to FFT.
  • FIG. 27 is a graph of a chronological arrangement of Z-axis acceleration data Kz for the Z-axis acceleration detection signal outputted from the Z-axis acceleration sensor 12 Z.
  • FIG. 28 shows the frequency analysis results obtained by subjecting the detected Z-axis acceleration data Kz in FIG. 27 to FFT.
  • FIG. 31 is a graph of a chronological arrangement of one example of the detected pulse wave data.
  • FIG. 32 shows the frequency analysis results obtained by subjecting the detected pulse wave data in FIG. 31 to FFT.
  • the MPU 24 sequentially reads the detected pulse wave data, the detected X-axis acceleration data, the detected Y-axis acceleration data, and the detected Z-axis acceleration data stored in the RAM 25 , and outputs the detected pulse wave data in a single sampling period to the synthesizer 43 .
  • the MPU 24 outputs the detected X-axis acceleration data Kx, the detected Y-axis acceleration data Ky, and the detected Z-axis acceleration data Kz corresponding to the detected pulse wave data outputted to the synthesizer 43 to the integrator 42 .
  • the filter coefficient generating section 41 generates the adaptive filter coefficient h based on the previously outputted data by the synthesizer 43 to which the filter has been applied.
  • the synthesizer 43 combines the current pulse wave data with the body motion removal data h(Kx 2 +Ky 2 +Kz 2 ), substantially removes (subtracts) the body motion components contained in the current detected pulse wave data, extracts the pulse wave components, and outputs the residual data, which is the data to which the adaptive filter has been applied.
  • FIG. 33 is a graph of a chronological arrangement of the residual data obtained by combining the data obtained by applying an adaptive filter to the combined acceleration vector data in FIG. 29 and the simulated low-frequency signal in FIG. 14 for the detected pulse wave data in FIG. 31.
  • the MPU 24 subjects the residual data to FFT.
  • FIG. 34 shows the frequency analysis results obtained by subjecting the residual data in FIG. 33 to FFT.
  • the frequency analysis results thus obtained retain spectra unrelated to the pulse wave components in a lower frequency range ( ⁇ 0.5 Hz) in comparison with the first embodiment, but they do not have any effect on the frequency band of the pulse wave components (2 Hz to 2.5 Hz). Therefore, the results have the body motion components originating in the veins substantially removed from the output signal of the pulse wave sensor (pulse wave components+body motion components), or, specifically, the results constitute pulse wave data corresponding primarily to the pulse wave components.
  • a pulse measurement device in a second alternative of the first embodiment is similar to the first embodiment, except that the use of a simulated low-frequency signal in the first embodiment is avoided in order to simplify the process and the device configuration, and that the use of combined acceleration vector data obtained by combining the Y-axis acceleration data and the Z-axis acceleration data is avoided as well. Therefore, the configuration in the second alternative of the first embodiment is essentially the same as the configuration of the pulse measurement device 10 shown in FIGS. 2 through 4, except that the MPU 24 is configured with an adaptive filter 50 of the second alternative instead of being configured with the adaptive filter 30 of the first embodiment.
  • FIG. 35 is a schematic structural block diagram of one example of an adaptive filter 50 according to the second alternative of the first embodiment.
  • the adaptive filter 50 has a filter coefficient generating section 51 and a synthesizer 52 .
  • a coefficient controller 51 A of the filter coefficient generating section 51 functions as a body motion component removing section and generates the adaptive filter coefficient h based on the data previously outputted from the synthesizer 52 to which the adaptive filter has been applied.
  • the filter coefficient generating section 51 applies the adaptive filter coefficient h generated by the coefficient controller 51 A to the X-axis acceleration data Kx, the Y-axis acceleration data Ky, and the Z-axis acceleration data Kz, which are the inputted body motion component detection signals; generates body motion removal data h(x), h(y), and h(z); and outputs the result to the synthesizer 52 .
  • FIG. 36 is a graph of a chronological arrangement of one example of detected pulse wave data.
  • FIG. 37 shows the frequency analysis results obtained by subjecting the detected pulse wave data in FIG. 36 to FFT.
  • FIG. 38 is a graph of a chronological arrangement of residual data obtained by combining the signals obtained by applying an adaptive filter to the combined acceleration vector signal in FIG. 29 and the simulated low-frequency signal in FIG. 14 for the detected pulse wave data in FIG. 31.
  • FIG. 39 shows the frequency analysis results obtained by subjecting the residual data in FIG. 38 to FFT.
  • the MPU 24 subjects the residual data e(n) to FFT, whereby, as shown in FIG. 34, the frequency analysis results thus obtained have the body motion components originating in the veins substantially removed from the output signal of the pulse wave sensor (pulse wave components+body motion components) similar to the first embodiment, or, specifically, the results constitute pulse wave data corresponding primarily to the pulse wave components. Also, in the second alternative of the first embodiment, the process and device configuration can be simplified because a simulated low-frequency signal is not used for processing.
  • a third alternative of the first embodiment is similar to the first alternative of the first embodiment except for dispensing with the use of a simulated low-frequency signal to conduct processing in the first alternative of the first embodiment (1.1). Therefore, the configuration in the third alternative of the first embodiment is essentially the same as the configuration of the pulse measurement device 10 shown in FIGS. 2 through 4, except that the MPU 24 is configured with an adaptive filter 60 of the third alternative instead of being configured with the adaptive filter 30 of the first embodiment.
  • FIG. 40 is a schematic structural block diagram of one example of the adaptive filter 60 according to the third alternative of the first embodiment.
  • the adaptive filter 60 has a filter coefficient generating section 61 and a synthesizer 62 .
  • a fourth alternative of the first embodiment is similar to the first embodiment, except for dispensing with use of a simulated low-frequency signal to conduct processing in the first embodiment. Therefore, the configuration in the fourth alternative of the first embodiment is essentially the same as the configuration of the pulse measurement device 10 shown in FIGS. 2 through 4, except that the MPU 24 is configured with an adaptive filter 70 of the fourth alternative instead of being configured with the adaptive filter 30 of the first embodiment.
  • FIG. 41 is a schematic structural block diagram of one example of the adaptive filter 70 according to the first embodiment.
  • the adaptive filter 70 has a filter coefficient generating section 71 and a synthesizer 72 .
  • a coefficient controller 71 A of the filter coefficient generating section 71 functions as a body motion component removing section that generates the adaptive filter coefficient h based on the data previously outputted from the synthesizer 72 to which the adaptive filter has been applied.
  • the following formula can be used when determining the combined acceleration vector data from the following three types of acceleration data: the X-axis acceleration data Kx, the Y-axis acceleration data Ky, and the Z-axis acceleration data Kz.
  • the X-axis acceleration data Kx, the Y-axis acceleration data Ky, and the Z-axis acceleration data Kz may similarly be suitably weighted and the adaptive filter coefficient may be applied thereto even when the combined acceleration vector data is not used, as in the second alternative of the first embodiment.
  • the simulated low-frequency signal may also be weighted.
  • a pulse measurement device 80 according to a second embodiment of the present invention will now be described with reference to FIGS. 42 through 60.
  • the main difference between the second embodiment and the first embodiment is that the body motion components are measured in the second embodiment using a pressure sensor instead of the triaxial acceleration sensor of the first embodiment. Otherwise the basic configuration is similar to the first embodiment; therefore, in view of the similarity between the first embodiment and the second embodiment, descriptions of the parts of the second embodiment with identical or similar functions to the parts of the first embodiment are omitted for the sake of simplicity.
  • the output of the pulse wave sensor for detecting pulse waves includes various body motion components in addition to pulse wave components. It is known that these body motion components are generated by changes in the body originating in the movements (walking/running, arm movement, and the like) of the user whose pulse is to be measured. Therefore, it is possible to detect the movements of the user when an acceleration sensor is used as the sensor for detecting body motion components, but the body motion components contained in the output of the pulse wave sensor are generated by changes in the body originating from these movements, and it is difficult to accurately detect the true body motion components contained in the output of the pulse wave sensor.
  • vein walls are highly extensible, they are stretched out when blood pressure increases, large quantities of blood accumulate in these sections, and this process is accompanied by an increase of pressure on the body surface along with the stretching of the veins.
  • the inventors have accordingly researched the relationship between the amount of change in pressure on the body surface and the amount of body motion components (amount of stroke components) included in the pulse wave sensor when the same body motion components are generated.
  • FIG. 42 is an explanatory diagram of the relationship between the amount of change in pressure and the amount of body motion components (amount of stroke components) included in the pulse wave sensor output. As shown in FIG. 42, it is clear that the amount of change in pressure and the amount of body motion components (amount of stroke components) included in the pulse wave sensor output have an essentially proportional relationship. In other words, it is possible to surmise the effect of the venous blood included in the output of the pulse wave sensor if the amount of change in pressure in the body surface can be detected.
  • the pulse rate is accurately detected based on a signal from which the effect of venous blood has been removed by detecting the stretching of the veins, or, specifically, the body motion components originating in the veins with an external pressure sensor, and subtracting them from the pulse wave sensor output at a specific rate.
  • FIG. 43 is a schematic structural diagram of a pulse measurement device 80 of the second embodiment.
  • the pulse measurement device 80 has a sensor module 81 mounted on the finger of the user, and a device main body 82 connected to the sensor module 81 via a wiring L and mounted on the arm of the user.
  • FIG. 44 is an explanatory diagram of the arrangement of sensors in the sensor module 81 .
  • the sensor module 81 is configured with a pulse wave sensor 83 for primarily detecting pulse wave components and a pressure sensor 84 for primarily detecting body motion components.
  • the pulse wave sensor 83 has an LED 83 A for emitting detection light and a PD (Photo Detector) 83 B for receiving the detection light reflected by the body.
  • LED 83 A for emitting detection light
  • PD Photo Detector
  • FIG. 45 is a schematic structural block diagram of the pulse measurement device 80 .
  • the pulse measurement device 80 has a pulse wave signal amplifying circuit 91 , a body motion signal amplifying circuit 92 , an A/D conversion circuit 93 , an MPU 94 , a RAM 95 , a ROM 96 , and a liquid crystal display device or other such display device 97 in addition to the pulse wave sensor 83 and the pressure sensor 84 previously described.
  • the pressure sensor 84 is used as the body motion sensor in the second embodiment.
  • the pulse wave signal amplifying circuit 91 amplifies the pulse wave detection signal outputted from the pulse wave sensor 83 at a prescribed rate of amplification, and outputs the result to the A/D conversion circuit 93 as an amplified pulse wave detection signal.
  • the body motion signal amplifying circuit 92 amplifies the pressure detection signal outputted from the pressure sensor 84 at a prescribed rate of amplification, and outputs the result to the A/D conversion circuit 93 as an amplified pressure detection signal.
  • the A/D conversion circuit 93 performs analog/digital conversion separately on the inputted amplified pulse wave detection signal and the amplified pressure detection signal, and outputs the result to the MPU 94 as detected pulse wave data and detected pressure data.
  • the MPU 94 stores the detected pulse wave data and the detected pressure data (detected body motion data) in the RAM 95 , calculates the pulse rate based on a control program stored in the ROM 96 , and displays the result on the display device 97 . More specifically, the MPU 94 chronologically arranges the detected pulse wave data and the detected pressure data (detected body motion data) stored in the RAM 95 , and determines the differential data, which is the difference between the detected pulse wave data and the detected pressure data, for each corresponding sampling time.
  • Frequency analysis FFT: Fast Fourier Transformation
  • the harmonic components of the pulse wave are extracted, and the pulse rate is calculated from the frequency.
  • FIG. 46 is a graph of a chronological arrangement of one example of detected pulse wave data.
  • FIG. 47 is a graph in which detected pressure data correlated with the detected pulse wave data in FIG. 46 is chronologically arranged along the same time axis.
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected pressure data stored in the RAM 95 and calculates the differential data by subtracting the detected pressure data in a certain sampling period from the detected pulse wave data for the same sampling timing.
  • FIG. 48 is a graph of a chronological arrangement of differential data calculated from the detected pulse wave data in FIG. 46 and the detected pressure data in FIG. 47.
  • the MPU 94 subjects the differential data to FFT.
  • FIG. 49 shows the frequency analysis results obtained by subjecting the differential data in FIG. 48 to FFT.
  • the frequency analysis results thus obtained have the body motion components originating in the veins substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor, and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • the MPU 94 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data constitute the pulse spectrum.
  • the MPU 94 then displays the pulse rate on the display device 97 .
  • variation in the veins which is the main factor in the body motion components generated in the body, can be accurately detected and registered by using a pressure sensor. Therefore, the body motion components can be accurately removed, making it possible to accurately detect pulse wave components, and hence to accurately measure the pulse rate.
  • a first alternative of the second embodiment is similar to the second embodiment, except that the second embodiment has a configuration in which the differential data is calculated by subtracting the detected pressure data from the detected pulse wave data prior to frequency analysis (FFT), while in the first alternative, the differential data is calculated after performing frequency analysis on the detected pulse wave data and the detected pressure data. Therefore, the configuration of the first alternative of the second embodiment is essentially the same as the configuration of the pulse measurement device 80 of the second embodiment shown in FIGS. 43 through 45.
  • the MPU 94 performs frequency analysis (FFT) on both the detected pulse wave data and the detected pressure data (detected body motion data) stored in the RAM 95 . Therefore, the MPU 94 essentially constitutes a first frequency analyzing section and a second frequency analyzing section.
  • FFT frequency analysis
  • the MPU 94 determines the differential data, which is the difference between the detected pulse wave data after analyzed for frequency and the detected pressure data after analyzed for frequency.
  • the harmonic components of the pulse wave are then extracted from the resulting differential data, and the pulse rate is calculated from the frequency thereof.
  • FIG. 50 is an explanatory diagram of the frequency analysis results for detected pulse wave data.
  • FIG. 51 is an explanatory diagram of the frequency analysis results for detected pressure data.
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected pressure data stored in the RAM 95 , and subjects them to FFT for frequency analysis.
  • FIG. 52 is an explanatory diagram of differential data, which is the difference between the detected pulse wave data after analyzed for frequency and the detected pressure data after analyzed for frequency.
  • the MPU 94 compares the detected pulse wave data after analyzed for frequency with the detected pressure data after analyzed for frequency, and determines the difference between these frequency components to create the differential data.
  • the frequency analysis results as the differential data have the body motion components originating in the veins substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor, and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • the MPU 94 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data constitute the pulse spectrum.
  • the MPU 94 then displays the pulse rate on the display device 97 .
  • variation in the veins which is the main factor in the body motion components generated in the body, can be also accurately detected and registered. Therefore, the body motion components can be accurately removed, making it possible to accurately detect the pulse wave components, and hence to accurately measure the pulse rate.
  • a second alternative of the second embodiment is similar to the second embodiment, except that the second embodiment has a configuration in which the differential data is calculated by subtracting the detected pressure data from the detected pulse wave data prior to frequency analysis (FFT), while in the second alternative, the MPU 94 is configured with an adaptive filter 100 and the body motion components are removed from the detected pulse wave data. Therefore, the second alternative of the second embodiment has the same configuration, except that the MPU 94 of the pulse measurement device 80 of the second embodiment is configured with an adaptive filter 100 .
  • FFT frequency analysis
  • FIG. 53 shows a schematic structural block diagram of one example of the adaptive filter 100 .
  • the adaptive filter 100 has a filter coefficient generating section 101 and a synthesizer 102 .
  • the filter coefficient generating section 101 functions as a body motion component removing section and generates the adaptive filter coefficient h based on data previously outputted by the synthesizer 102 to which the filter has been applied.
  • FIG. 54 is a graph of a chronological arrangement of an example of the detected pulse wave data.
  • FIG. 55 is a graph in which detected pressure data correlated with the detected pulse wave data in FIG. 54 is chronologically arranged along the same time axis.
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected pressure data stored in the RAM 95 , and outputs the detected pulse wave data in a certain sampling period to the synthesizer 102 .
  • the MPU 94 presents the filter coefficient generating section 101 with detected pressure data that corresponds to the detected pulse wave data outputted to the synthesizer 102 .
  • the filter coefficient generating section 101 creates an adaptive filter coefficient h based on the data previously outputted from the synthesizer 102 to which the adaptive filter has been applied.
  • FIG. 56 is a graph of a chronological arrangement of residual data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 54 and the detected pressure data in FIG. 55.
  • the MPU 94 subjects the residual data to FFT.
  • FIG. 57 shows the frequency analysis results obtained by subjecting the residual data in FIG. 56 to FFT.
  • the frequency analysis results thus obtained have the body motion components originating in the veins substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor, and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • the MPU 94 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data that primarily contains pulse wave components constitute the pulse spectrum.
  • the MPU 94 then displays the pulse rate on the display device 97 .
  • variation in the veins which is the main factor in the body motion components generated in the body, can be also accurately detected and registered. Therefore, the body motion components can be accurately removed, making it possible to accurately detect the pulse wave components, and hence to accurately measure the pulse rate.
  • a third alternative of the second embodiment is an alternative in the sense that the sensor module 81 has both the pulse wave sensor 83 and the pressure sensor 84 in the second embodiment, while in the third alternative, the sensor module 81 is divided into a sensor module 111 A and a sensor module 111 B, and the pulse wave sensor 83 and pressure sensor 84 are mounted on separate fingers.
  • the configuration of a pulse measurement device 110 in the third alternative of the second embodiment is the same as the pulse measurement device 80 of the second embodiment.
  • FIG. 58 is a schematic structural block diagram of a pulse measurement system according to the third alternative of the second embodiment.
  • the pulse measurement device 110 has a sensor module 111 A mounted on a first finger of the user, a sensor module 111 B mounted on a second finger of the user, and a device main body 112 that is connected to the sensor module 111 A via a wiring L 1 , is also connected to the sensor module 111 B via a wiring L 2 , and is mounted on the arm of the user.
  • FIG. 59 is an explanatory diagram of the arrangement of sensors in the sensor module 111 A.
  • the sensor module 111 A has the pressure sensor 84 for primarily detecting body motion components.
  • FIG. 60 is an explanatory diagram of the arrangement of the sensors in the sensor module 111 B.
  • the sensor module 111 B has the pulse wave sensor 83 for primarily detecting pulse wave components.
  • the pulse wave sensor 83 has the LED 83 A for emitting detection light, and the PD (Photo Detector) 83 B for receiving the detection light reflected by the body.
  • measurement is taken with the pressure sensor 84 for primarily detecting body motion components and with the pulse wave sensor 83 for primarily detecting pulse wave components, mounted on separate fingers, so it is possible to reduce the effect of the mechanical arrangement of the other sensor and the effect of noise on the output signal due to the output signal of the other sensor.
  • the pressure sensor 84 was provided either adjacent to or separate from the pulse wave sensor 83 , but it is also possible to use a configuration in which the pressure sensor 84 is disposed in a substantially layered state over the pulse wave sensor 83 in a direction away from the body.
  • a pulse measurement device 120 according to a third embodiment of the present invention will now be described with reference to FIGS. 61 through 81.
  • the main difference between the third embodiment and the second embodiment is that in the second embodiment, venous blood pressure is detected using the pressure sensor 84 , while in the third embodiment, venous blood pressure is estimated by detecting the relative difference in the vertical direction between the position of the heart of the user and the mounted position of the pulse meter with the aid of an angle sensor 122 .
  • the basic configuration is similar to the first embodiment or the second embodiment, therefore, in view of the similarity between the first/second embodiment and the third embodiment, descriptions of the parts of the third embodiment with identical or similar functions to the parts of the first/second embodiment are omitted for the sake of simplicity.
  • the second embodiment is configured to detect venous blood pressure with a pressure sensor in order to detect body motion components originating in venous blood.
  • the third embodiment focuses on the concept that the relative difference in the vertical direction between the position of the heart of the user and the mounted position of the pulse meter has a proportional relationship with the vein meter pressure.
  • the third embodiment is designed for a case in which the relative difference in the vertical direction between the position of the heart of the user and the mounted position of the pulse meter is detected as an angle about the shoulder joint of the arm on which the pulse meter is mounted (for example, 0° when the arm hangs straight down, and 90° when the arm is horizontal).
  • FIG. 61 is an explanatory diagram of the relationship between the amount of change in height of the arm and the amount of body motion components (amount of stroke components) included in the pulse wave sensor output. As shown in FIG. 61, it is clear that the amount of change in height of the arm and the amount of body motion components (amount of stroke components) included in the pulse wave sensor output have a substantially proportional relationship. In other words, it is possible to surmise the effect of venous blood included in the pulse wave sensor output if the amount of change in height of the arm can be detected.
  • FIG. 62 is an explanatory diagram of the relationship between the angle and direction of the arm.
  • the angle of the arm is 0° and the direction is down when the arm hangs straight down
  • the angle of the arm is 90° and the direction is middle when the arm is horizontal
  • the angle of the arm is 180° and the direction is up when the arm is extended straight up.
  • the direction is slanted down when the arm is intermediate between the position of the arm hanging straight down and the position of the arm being horizontal
  • the direction is slanted up when the arm is intermediate between the position of the arm being horizontal and the position of the arm extending straight up.
  • FIG. 63 is an explanatory diagram of the relationship between the amount of change in height of the arm position (direction of the arm) in its initial state and the amount of body motion components (amount of stroke components) as an angle sensor output.
  • the change in the amount of body motion components (amount of stroke components) which is the output of the angle sensor, displays the same tendency with any direction of the arm even if the height of the position of the arm is varied.
  • FIG. 64 is an explanatory diagram of the change in the amount of body motion components (stroke components) as the angle sensor output due to the position of the arm when the amount of change in height is fixed. As seen in FIG. 64, it is clear that the amount of body motion components as the angle sensor output is low when the angle of the arm is greater than 90°.
  • the angle sensor output shall be corrected when the angle of the arm is greater than 90°.
  • FIG. 65 is an explanatory diagram of the relationship between the amount of change in height of the position of the arm (direction of the arm) in its initial state and the amount of body motion components (stroke components) included in the angle sensor output after correction. This case involves the example in FIG. 63, in which the amount of body motion components (amount of stroke components) Y corresponding to the angle sensor output is corrected by the angle X of the arm according to the following formula when the angle of the arm is greater than 90°.
  • y is the amount of change in height (mV)
  • X is the angle (degree)
  • Y is the amount of change in height (mV) after correction.
  • the relative difference in the vertical direction between the position of the heart of the user and the mounted position of the pulse meter is detected by an external angle sensor, and the body motion components originating in the veins are subtracted from the pulse wave sensor output at a specific rate, whereby the pulse rate is accurately detected based on a signal from which the effect of venous blood has been removed.
  • FIG. 66A is a cross-sectional view of the pulse measurement device 120 wherein the pulse meter of the third embodiment is incorporated into a watchcase.
  • the pulse wave sensor 83 and an angle sensor 122 are provided on the reverse surface of a watchcase 121 of the pulse measurement device 120 .
  • the pulse wave sensor 83 described above is formed integrally with the main body on the reverse side of the watchcase 121 .
  • the watchcase 121 is provided with a wristband 123 for arm mounting, and the reverse side of the watchcase 121 is pressed against the back of the wrist when the wristband 123 is mounted by being wound around the wrist.
  • the reverse side of the watchcase 121 is provided with transparent glass 83 C as a component of the pulse wave sensor 83 .
  • the transparent glass 83 C is fixed to the watchcase 121 by a back lid 124 .
  • the transparent glass 83 C protects the LED 83 A and the PD 83 B, which are components of the pulse wave sensor 83 , and also transmits the light incident on the LED 13 C and reflected light obtained via the body, and directs the light to the PD 83 B.
  • the front side of the watchcase 121 is provided with a liquid crystal display device or another such display device 97 for displaying the pulse rate HR and other such living organism information based on the detection results from the pulse wave sensor 83 in addition to the current time and date. Also, the interior of the watchcase 121 has a CPU and other such IC circuits on a main board 126 , whereby a data processing circuit 127 is configured.
  • the reverse side of the main board 126 is provided with a battery 128 , and the battery 128 supplies power to the display device 97 , the main board 126 , and the pulse wave sensor 83 .
  • the main board 126 and the pulse wave sensor 83 are designed to be connected by a heat seal 129 , wherein power is supplied to the pulse wave sensor 83 and the angle sensor 122 from the main board 126 , the pulse wave detection signal is fed to the main board 126 from the pulse wave sensor 83 , and the angle detection signal is fed from the angle sensor 122 by a wiring formed by the heat seal 129 .
  • the data processing circuit 127 subjects the pulse wave signal to FFT and calculates the pulse rate HR by analyzing the processing results thereof.
  • the external surface of the watchcase 121 is provided with button switches (not shown) for time setting, display mode switching, and the like.
  • the reverse side of the watchcase 121 faces the back of the wrist when the wristband 123 is wound around the wrist. Therefore, the light from the LED 83 A is directed to the back of the wrist via the transparent glass 83 C, and the reflected light is received by the PD 83 B.
  • the angle sensor 122 outputs an angle detection signal used to determine the relative difference in the vertical direction between the position of the heart of the user and the mounted position of the pulse meter. Therefore, the angle sensor 122 essentially constitutes a difference detecting section.
  • a differential capacitive sensor 122 A or a rotary-spindle angle sensor 122 B is preferably used as the angle sensor 122 .
  • FIG. 67 is a structural schematic diagram of the differential capacitive sensor 122 A used as the angle sensor.
  • FIG. 68 is a partial enlarged diagram of the differential capacitive sensor 122 A before acceleration is applied.
  • the differential capacitive sensor 122 A is a biaxial acceleration sensor and has a first sensitivity axis LX 1 and a second sensitivity axis LX 2 .
  • the differential capacitive sensor 122 A has flexible tethers 132 supported by a pair of fixed shafts 131 .
  • the tethers 132 support a beam 133 from both sides.
  • the beam 133 is provided with an electrode 133 A protruding from the side, which is held by a pair of fixed external electrodes 134 A and 134 B so as to face both fixed external electrodes 134 at a position virtually equidistant from the fixed external electrodes 134 A and 134 B.
  • the electrode 133 A and the fixed external electrodes 134 A and 134 B each function as capacitors with roughly the same capacitance.
  • FIG. 69 is a partial enlarged diagram of a differential capacitive sensor to which acceleration has been applied.
  • the differential capacitive sensor 122 A when the differential capacitive sensor 122 A is tilted, the tethers 132 bend due to gravitational acceleration, resulting in the state shown in FIG. 69.
  • the distance G1 between the electrode 133 A and the fixed external electrode 134 A becomes greater than the distance G2 between the electrode 133 A and the fixed external electrode 134 B, as shown in FIG. 69.
  • the capacitance of the capacitor configured by the electrode 133 A and the fixed external electrode 134 B becomes greater. Therefore, since this difference in capacitance is proportional to the extent of gravitational acceleration, or, specifically, to the angle of inclination, it is possible to detect the angle by measuring the difference in capacitance.
  • FIG. 70 is a front view of the rotary-spindle angle sensor 122 B used as the angle sensor.
  • FIG. 71 is a side view of the rotary-spindle angle sensor 122 B in FIG. 70.
  • the rotary-spindle angle sensor 122 B has a supporting axle 141 , a rotary spindle 142 rotatably supported by the supporting axle 141 , a slitted plate 143 that rotates uniformly with the rotary spindle 142 and has two groups of slits formed with different phases, a fixed plate 144 for holding the supporting axle 141 , and an optical sensor unit 145 disposed in a position on the fixed plate 144 facing the slitted plate 143 .
  • the optical sensor unit 145 outputs an angle detection signal with a pulse rate corresponding to the amount of rotations of the slitted plate 143 for each group of slits when the rotary spindle 142 rotates due to a change in the angle. At this point it is also possible to detect the changing direction of the angle because the phase relationship of the angle detection signals for both groups of slits differs in terms of the rotating direction of the rotary spindle.
  • FIG. 72 is a graph of a chronological arrangement of one example of detected pulse wave data.
  • FIG. 73 shows the frequency analysis results obtained by subjecting the detected pulse wave data in FIG. 72 to FFT.
  • FIG. 74 is a graph of a chronological arrangement of one example of detected angle data.
  • FIG. 75 shows the frequency analysis results obtained by subjecting the detected angle data in FIG. 74 to FFT.
  • the configuration as a pulse measurement device is essentially the same as the second embodiment, and will now be described with reference to the schematic structural block diagram in FIG. 66B.
  • the body motion sensor 122 is an angle sensor.
  • the MPU 94 has the functions of the adaptive filter 100 ′ shown in FIG. 66C.
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected angle data stored in the RAM 95 , and outputs the detected pulse wave data in a certain sampling period to the synthesizer 102 .
  • the MPU 94 also presents the filter coefficient generating section 101 with detected angle data that corresponds to the detected pulse wave data.
  • the filter coefficient generating section 101 generates the adaptive filter coefficient h based on the data previously outputted by the synthesizer 102 to which the filter has been applied.
  • FIG. 76 is a graph of a chronological arrangement of residual data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 72 and the detected angle data in FIG. 74.
  • the MPU 94 subjects the residual data in FIG. 76 to FFT.
  • FIG. 77 shows the frequency analysis obtained by subjecting the residual data in FIG. 76 to FFT.
  • the frequency analysis results thus obtained have the body motion components originating in the veins substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor, and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • the MPU 94 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data that primarily contains pulse wave components constitute the pulse spectrum SP 1 .
  • the MPU 94 then displays the pulse rate on the display device 97 .
  • FIG. 78 is a graph of a chronological arrangement of one example of corrected detected angle data.
  • FIG. 79 shows the frequency analysis obtained by subjecting the corrected detected angle data in FIG. 78 to FFT.
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected angle data stored in the RAM 95 , outputs the detected pulse wave data in a certain sampling period to the synthesizer 102 , and outputs the corrected detected angle data that corresponds to the detected pulse wave data to the filter coefficient generating section 101 .
  • the filter coefficient generating section 101 creates the adaptive filter coefficient h based on the data previously outputted by the synthesizer 102 to which the filter has been applied.
  • FIG. 80 is a graph of a chronological arrangement of residual data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 72 and the corrected detected angle data in FIG. 78.
  • the MPU 94 subjects this residual data to FFT.
  • FIG. 81 shows the frequency analysis results obtained by subjecting the residual data in FIG. 80 to FFT.
  • FIG. 81 it is clear from the frequency analysis results thus obtained that although the frequency analysis results and the height of the peak on the pulse spectrum SP 1 shown in FIG. 77 do not change, the height of the peaks of other spectra is suppressed, and the MPU 94 can more accurately calculate the pulse rate from the frequency on the assumption that the maximum frequency components of the pulse wave data constitute the pulse spectrum SP 1 .
  • variation in the veins which is the main factor in the body motion components generated in the body, can be more accurately detected and registered, particularly when angle correction is performed. Therefore, the body motion components can be accurately removed, making it possible to accurately detect pulse wave components, and hence to accurately measure the pulse rate.
  • the angle sensor 122 was provided adjacent to or separate from the pulse wave sensor 83 , but it is also possible to use a configuration in which the angle sensor 122 is disposed in a substantially layered state over the pulse wave sensor 83 in a direction away from the body.
  • the third embodiment described a case in which the control program is stored in the ROM 96 in advance, but another possibility is a configuration in which the control program is stored in advance on various magnetic disks, optical disks, memory cards, and other such storage media, and is read from these storage media and installed. Another possibility is a configuration in which a communication interface is provided for downloading the control program via the Internet, LAN, or another such network; installing the program; and running this program.
  • a pulse measurement device 190 according to a fourth embodiment of the present invention will now be described with reference to FIGS. 82 through 109.
  • the main difference between the second embodiment and the fourth embodiment is that the fourth embodiment uses a configuration in which, instead of using the pressure sensor 84 of the second embodiment, body motion components are estimated using a blood vessel simulation sensor 150 , 160 , 170 , or 180 for simulating the movement of venous blood, and these body motion components are removed from the output signal of the pulse wave sensor.
  • the basic configuration is similar to that of the second embodiment; therefore, in view of the similarity between the second embodiment and the fourth embodiment, descriptions of the parts of the fourth embodiment with identical or similar functions to the parts of the second embodiment may be omitted for the sake of simplicity.
  • the output of the pulse wave sensor for detecting pulse waves includes various body motion components in addition to pulse wave components.
  • These body motion components are known to be generated by changes in the body originating in the movements (walking/running, arm movement, and the like) of the user whose pulse is to be measured, and, as described above, means in which detection light from an LED, which is a light-emitting element, is directed into the body, and reflected light is received by a PD (Photo Detector), which is a light receiving element, is used as the means for detecting the body motion components inside the body.
  • PD Photo Detector
  • the detection light directed into the body is absorbed and scattered by arteriolovenous blood flowing near the skin and by the body tissue
  • the change in the amount of detection light received by the PD at rest in the absence of movement is primarily determined by the change in arterial blood due to pulsation
  • absorbed light components due to venous blood and tissues are substantially constant.
  • the fourth embodiment involves estimating the body motion components by focusing on the movement of venous blood and simulating the movement of venous blood when the body motion components in the body are to be removed, and removing the body motion components from the output signal of the pulse wave sensor.
  • FIG. 82 is a diagram illustrating the principle of a blood vessel simulation sensor mounted on the body and designed for simulating the movement (behavior) of venous blood.
  • venous blood Compared to arterial blood, venous blood has low blood pressure and is therefore susceptible to the effect of inertial force due to gravity and arm movements. Therefore, as shown in FIG. 82, a solution LQ with a specific viscosity is sealed inside a cylindrical sealed container that models a blood vessel in the peripheral direction, whereby it is possible to estimate the body motion (behavior) of venous blood by observing the body motion (behavior) of the solution from the outside, and the body motion components generated in the body can be observed from the estimated movement of venous blood.
  • the movement of the solution sealed inside a cylindrical sealed container is detected by a pressure sensor, an optical sensor or another such sensor, and body motion components generated in the body are detected based on the output signal of this sensor.
  • the pulse rate is accurately detected based on the signal from which the effect of venous blood has been removed.
  • the embodiments of the blood vessel simulation sensor are classed into a rigid type, an elastic type, and an acceleration sensor type.
  • the rigid type is a sensor in which a solution with a viscosity (for example, 1 to 100 cP) that exhibits the same behavior as blood is sealed in a rigid cylindrical container.
  • the elastic type is a sensor in which a resilient tube is closed off at both ends and a solution with a viscosity (for example, 1 to 100 cP) that exhibits the same behavior as blood is sealed in the tube.
  • the blood vessel simulation sensor of the acceleration sensor type is one in which the acceleration sensor in FIG. 82 whose direction of sensitivity is the peripheral direction is used as a blood vessel simulation sensor.
  • FIG. 83 is a schematic diagram of a first rigid type of blood vessel simulation sensor 150 .
  • the blood vessel simulation sensor 150 has a resinous (plastic) casing 151 closed off at both ends, and simulation blood 152 whose viscosity is set to ensure a behavior similar to that of venous blood is sealed in the casing 151 inside the sensor.
  • a pressure sensor (behavior detection sensor) 153 for detecting pressure changes in accordance with the movement of the simulation blood 152 is provided to one end of the casing 151 in the longitudinal direction.
  • FIG. 84 is a schematic diagram of a second rigid type of blood vessel simulation sensor 160 .
  • the blood vessel simulation sensor 160 has a resinous (plastic) casing 161 closed off at both ends, and simulation blood 162 whose viscosity is set to ensure a behavior similar to that of venous blood is sealed in the casing 161 inside the sensor.
  • an optical sensor (behavior detection sensor) 163 for detecting the state of movement of the simulation blood 162 is provided to the sidewall of the casing 161 .
  • the optical sensor 163 has an LED 164 for emitting detection light and a PD 165 for receiving the detection light.
  • the simulation blood 162 is colored the same as the detection light, and the optical sensor 163 detects changes in the state of the liquid surface.
  • FIG. 85 is a schematic diagram of a first elastic type of blood vessel simulation sensor 170 .
  • the blood vessel simulation sensor 170 has a resinous (plastic) casing 171 closed off at both ends, and simulation blood 172 whose viscosity is set to ensure a behavior similar to that of venous blood is sealed in the casing 171 inside the sensor.
  • a pressure sensor (behavior detection sensor) 173 for detecting pressure changes in accordance with the movement of the simulation blood 172 is provided to one end of the casing 171 in the longitudinal direction.
  • FIG. 86 is a schematic diagram of a second elastic type of blood vessel simulation sensor 180 .
  • the blood vessel simulation sensor 180 has a resilient resinous casing 181 made of rubber or the like and closed off at both ends, and simulation blood 182 whose viscosity is set to ensure a behavior similar to that of venous blood is sealed in the casing 181 inside the sensor.
  • a pressure sensor (behavior detection sensor) 183 for detecting pressure changes in accordance with the movement of the simulation blood 182 is provided to the sidewall of the casing 181 .
  • FIG. 87 is an explanatory diagram of the relationship between the rigid type of blood vessel simulation sensor 150 or 160 and the body motion components (stroke components) included in the output of the pulse wave sensor 83 . As shown in FIG. 87, it is clear that the output of the rigid type of blood vessel simulation sensor 150 or 160 has a substantially proportional correlation with the size of the body motion components (stroke components) included in the output of the pulse wave sensor 83 .
  • FIG. 88 is an explanatory diagram of the relationship between the elastic type of blood vessel simulation sensor 170 or 180 and the body motion components (stroke components) included in the output of the pulse sensor 83 . As shown in FIG. 88, it is clear that the output of the elastic type of blood vessel simulation sensor 170 or 180 has a substantially proportional correlation with the size of the body motion components (stroke components) included in the output of the pulse wave sensor 83 , similar to the output of the rigid type of blood vessel simulation sensor 150 or 160 .
  • FIG. 89 is a schematic structural block diagram of a pulse measurement device 190 of the fourth embodiment.
  • the pulse measurement device 190 has a sensor module 191 mounted on the finger of the user, and a device main body 192 connected to the sensor module 191 via a wiring LN and mounted on the arm of the user.
  • FIG. 90 is an explanatory diagram of the arrangement of the sensors in the sensor module in a mounted state.
  • the sensor module 191 is configured with a pulse wave sensor 83 for primarily detecting pulse wave components and a blood vessel simulation sensor described above for primarily detecting body motion components.
  • the first rigid type of blood vessel simulation sensor 150 is used as the blood vessel simulation sensor.
  • the first rigid type of blood vessel simulation sensor 150 is disposed near the pulse wave sensor 83 and is also disposed in a substantially layered state over the pulse wave sensor 83 in a direction away from the user (the body).
  • the pulse wave sensor 83 referred to herein has an LED 83 A for emitting detection light and a PD 83 B for receiving the detection light reflected by the body.
  • FIG. 91 is a schematic structural block diagram of the pulse measurement device 190 .
  • the pulse measurement device 190 has, in addition to the pulse wave sensor 83 described above, a blood vessel simulation sensor 150 as a body motion sensor, a pulse wave signal amplifying circuit 91 , a body motion signal amplifying circuit 92 , an A/D conversion circuit 93 , an MPU 94 , a RAM 95 , a ROM 96 , and a display device 97 .
  • the pulse wave signal amplifying circuit 91 amplifies the pulse wave detection signal outputted from the pulse wave sensor 83 at a prescribed rate of amplification, and outputs the result as an amplified pulse wave detection signal to the A/D conversion circuit 93 .
  • the body motion signal amplifying circuit 92 amplifies the pressure detection signal based on the movement of the simulation blood 152 and outputted from the first rigid type of blood vessel simulation sensor 150 functioning as a body motion sensor at a specific rate, and outputs the result as an amplified pressure detection signal to the A/D conversion circuit 93 .
  • the A/D conversion circuit 93 performs analog/digital conversion separately on the inputted amplified pulse wave detection signal and the amplified pressure detection signal, and outputs the result as detected pulse wave data and detected pressure data to the MPU 94 .
  • the MPU 94 stores the detected pulse wave data and detected pressure data (detected body motion data) for the pressure detection signal outputted from the first rigid type of blood vessel simulation sensor 150 in the RAM 95 , calculates the pulse rate based on a control program stored in the ROM 96 , and displays the result on the display device 97 .
  • the MPU 94 chronologically arranges the detected pulse wave data and the detected pressure data (detected body motion data) stored in the RAM 95 and determines the differential data, which is the difference between the detected pulse wave data and the detected pressure data for each corresponding sampling time.
  • Frequency analysis FFT: Fast Fourier Transformation
  • the harmonic components of the pulse wave are extracted, and the pulse rate is calculated from the frequency.
  • FIG. 92 is a graph of a chronological arrangement of one example of the detected pulse wave data.
  • FIG. 93 is a graph in which detected pressure data correlated with the detected pulse wave data in FIG. 92 is chronologically arranged along the same time axis.
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected pressure data stored in the RAM 95 and calculates the differential data by subtracting the detected pressure data in a certain sampling period from the detected pulse wave data at the same sampling timing.
  • FIG. 94 is a graph of a chronological arrangement of differential data calculated from the detected pulse wave data in FIG. 92 and the detected pressure data in FIG. 93.
  • the MPU 94 subjects the differential data to FFT.
  • FIG. 95 shows the frequency analysis results obtained by subjecting the differential data in FIG. 94 to FFT.
  • the frequency analysis results thus obtained have the body motion components originating in the veins substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor 83 , and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • the MPU 94 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data constitute the pulse spectrum PH 1 .
  • the MPU 94 then displays the pulse rate on the display device 97 .
  • variation in the veins which is the main factor in the body motion components generated in the body, can be accurately estimated based on the output signal from the blood vessel simulation sensor. Therefore, the body motion components can be accurately removed, making it possible to accurately detect pulse wave components, and hence to accurately measure the pulse rate.
  • the fourth embodiment describes the first rigid type of blood vessel simulation sensor 150 used as the rigid type of blood vessel simulation sensor, but the second rigid type of blood vessel simulation sensor 160 may also be used.
  • a first alternative of the fourth embodiment is similar to the fourth embodiment except that the fourth embodiment uses a configuration in which differential data is calculated by subtracting detected pressure data, which corresponds to the pressure detection signal outputted from the first rigid type of blood vessel simulation sensor 150 , from the detected pulse wave data prior to frequency analysis (FFT), while the first alternative uses a configuration in which the differential data is calculated after frequency analysis is performed on the detected pulse wave data and on the detected pressure data that corresponds to the pressure detection signal outputted from the first rigid type of blood vessel simulation sensor 150 .
  • FFT frequency analysis
  • the MPU 94 performs frequency analysis (FFT) separately on the detected pulse wave data and the detected pressure data (detected body motion data) that corresponds to the pressure detection signal outputted from the first rigid type of blood vessel simulation sensor 150 stored in the RAM 95 .
  • FFT frequency analysis
  • the MPU 94 determines the differential data, which is the difference between the detected pulse wave data after analyzed for frequency and the detected pressure data after analyzed for frequency.
  • the harmonic components of the pulse wave are then extracted from the resulting differential data, and the pulse rate is calculated from the frequency thereof.
  • FIG. 96 is an explanatory diagram of the frequency analysis results for detected pulse wave data.
  • FIG. 97 is an explanatory diagram of the frequency analysis results for detected pressure data that corresponds to the pressure detection signal outputted from the first rigid type of blood vessel simulation sensor 150 .
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected pressure data stored in the RAM 95 , and subjects them to FFT.
  • FIG. 98 is an explanatory diagram of differential data, which is the difference between the detected pulse wave data after analyzed for frequency and the detected pressure data after analyzed for frequency.
  • the MPU 94 compares the detected pulse wave data after analyzed for frequency with the detected pressure data after analyzed for frequency, and determines the difference between these frequency components to create the differential data.
  • the frequency analysis results thus obtained as the differential data have the body motion components originating in the veins substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor, and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • the MPU 94 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data constitute the pulse spectrum PH 1 .
  • the MPU 94 then displays the pulse rate on the display device 97 .
  • a second alternative of the fourth embodiment is similar to the fourth embodiment except that the fourth embodiment uses a configuration in which differential data is calculated by subtracting detected pressure data, which corresponds to the pressure detection signal outputted from the first rigid type of blood vessel simulation sensor 150 , from the detected pulse wave data prior to frequency analysis (FFT), while the second alternative uses a configuration in which the MPU 94 has an adaptive filter 200 , and the body motion components that correspond to the pressure detection signal outputted from the blood vessel simulation sensor 150 are removed from the detected pulse wave data.
  • FFT frequency analysis
  • FIG. 99 is a schematic structural block diagram of one example of the adaptive filter 200 .
  • the adaptive filter 200 has a filter coefficient generating section 201 and a synthesizer 202 .
  • the filter coefficient generating section 201 functions as a body motion component removing section and generates the adaptive filter coefficient h based on data previously outputted by the synthesizer 202 to which the filter has been applied.
  • FIG. 100 is a graph of a chronological arrangement of an example of the detected pulse wave data.
  • FIG. 101 is a graph in which the detected pressure data inputted from the blood vessel simulation sensor and correlated with the detected pulse wave data in FIG. 100 is chronologically arranged along the same time axis.
  • the MPU 94 sequentially reads out the detected pulse wave data and the detected pressure data stored in the RAM 95 , and outputs the detected pulse wave data in a certain sampling period to the synthesizer 202 .
  • the MPU 94 presents the filter coefficient generating section 201 with detected pressure data that corresponds to the detected pulse wave data.
  • the filter coefficient generating section 201 creates an adaptive filter coefficient h based on the data previously outputted from the synthesizer 202 to which the adaptive filter has been applied.
  • FIG. 102 is a graph of a chronological arrangement of residual data obtained by applying an adaptive filter to the detected pulse wave data in FIG. 100 and the detected pressure data outputted from the blood vessel simulation sensor in FIG. 101.
  • the MPU 94 subjects the residual data to FFT.
  • FIG. 103 shows the frequency analysis results obtained by subjecting the residual data in FIG. 102 to FFT.
  • the frequency analysis results thus obtained have the body motion components originating in the veins, which are estimated based on the blood vessel simulation sensor output, substantially removed from the output signal (pulse wave components+body motion components) of the pulse wave sensor, and are, specifically, pulse wave data that primarily corresponds to the pulse wave components.
  • the MPU 94 calculates the pulse rate from the frequency on the assumption that the maximum frequency components of the resulting pulse wave data that primarily contains pulse wave components constitute the pulse spectrum.
  • the MPU 94 then displays the pulse rate on the display device 97 .
  • variation in the veins which is the main factor of the body motion components generated in the body, can be surely estimated with a blood vessel simulation sensor, whereby the body motion components can be accurately removed, making it possible to surely detect pulse wave components, and hence to accurately measure the pulse rate.
  • a third alternative of the fourth embodiment will now be described.
  • the third alternative of the fourth embodiment is similar to the fourth embodiment, except that the sensor module 191 having the rigid type of blood vessel simulation sensor 150 in the fourth embodiment is replaced by a sensor module 191 A having a resilient type of blood vessel simulation sensor 170 .
  • FIG. 104A is an explanatory diagram of the arrangement of sensors in the sensor module 191 A in a mounted state.
  • FIG. 104B is a schematic structural block diagram of the pulse measurement device according to the third alternative of the fourth embodiment.
  • the sensor module 191 A is configured to include the pulse wave sensor 83 for primarily detecting pulse wave components, and the first resilient type of blood vessel simulation sensor 170 described above for primarily detecting body motion components.
  • Such a configuration makes it possible to surely estimate body motion components generated in the body and to remove the body motion components in a more similar to the actual veins.
  • the third alternative of the fourth embodiment describes the use of the first elastic type of blood vessel simulation sensor 170 as an elastic type of blood vessel simulation sensor, but a second elastic type of blood vessel simulation sensor 180 may also be used.
  • the fourth alternative of the fourth embodiment is similar to the fourth embodiment, except that the sensor module 191 having the rigid type of blood vessel simulation sensor 150 in the fourth embodiment is replaced by a sensor module 191 B having an acceleration sensor 210 as a blood vessel simulation sensor.
  • FIG. 105A is an explanatory diagram of the arrangement of sensors in the sensor module 191 B in a mounted state.
  • FIG. 105B is a schematic structural block diagram of the pulse measurement device according to the fourth alternative of the fourth embodiment.
  • the sensor module 191 B is configured having a pulse wave sensor 83 for primarily detecting pulse wave components, and the acceleration sensor 210 for primarily detecting acceleration in the peripheral direction shown in FIG. 82.
  • the acceleration sensor 210 as the blood vessel simulation sensor is disposed near the pulse wave sensor 83 and is also disposed in a substantially layered state over the pulse wave sensor 83 in a direction away from the user (the body).
  • FIG. 106 is an explanatory diagram of the relationship between acceleration in the direction of the X-axis described hereinbelow when a triaxial (X, Y, Z-axes) acceleration sensor is used as the acceleration sensor, and the body motion components (stroke components) included in the output signal of the pulse wave sensor 83 .
  • FIG. 107 is an explanatory diagram of the relationship between acceleration in the direction of the Y-axis described hereinbelow when a triaxial acceleration sensor described hereinbelow is used as the acceleration sensor, and the body motion components (stroke components) included in the output signal of the pulse wave sensor 83 .
  • FIG. 108 is an explanatory diagram of the relationship between acceleration in the direction of the Z-axis described hereinbelow when a triaxial (X, Y, Z-axes) acceleration sensor described hereinbelow is used as the acceleration sensor, and the body motion components (stroke components) included in the output signal of the pulse wave sensor 83 .
  • FIG. 109 is an explanatory diagram of the three axes.
  • the X-axis extends in the peripheral direction (direction of the fingertips) shown in FIG. 82
  • the Y-axis is perpendicular to and lies in the same plane as the X-axis when the palm of the hand is aligned in this plane
  • the Z-axis is perpendicular to the plane containing the palm of the hand.
  • the body motion components contained in the output signal of the pulse wave sensor 83 are primarily based on components in the X-axis direction. Therefore, it is possible to estimate the body motion components detected by the pulse wave sensor 83 if a uniaxial acceleration sensor capable of detecting acceleration only in the X-axis direction, or, specifically, in the peripheral direction shown in FIG. 82, is used as the acceleration sensor 210 .
  • a pulse measurement device 220 according to a fifth embodiment of the present invention will now be described with reference to FIGS. 110 and 111.
  • the main difference between the fourth embodiment and the fifth embodiment is that in the fourth embodiment, the pulse wave sensor 83 and the blood vessel simulation sensor 150 are configured integrally as the sensor module 191 , while in the fifth embodiment, the blood vessel simulation sensor 150 is incorporated into the main body of the device. Otherwise the basic configuration is similar to the fourth embodiment; therefore, in view of the similarity between the fourth embodiment and the fifth embodiment, descriptions of the parts of the fifth embodiment with identical or similar functions to the parts of the fourth embodiment may be omitted for the sake of simplicity.
  • FIG. 110 is an external perspective view of the pulse measurement device 220 of the fifth embodiment.
  • FIG. 111 is a cross-sectional view of a sensor module 221 in FIG. 110.
  • the pulse measurement device 220 has the sensor module 221 mounted on the finger of the user, and a device main body 222 connected to the sensor module 221 via a wiring LN and mounted on the arm of the user.
  • the sensor module 221 is configured having a pulse wave sensor 83 for primarily detecting pulse wave components.
  • the pulse wave sensor 83 has an LED 83 A for emitting detection light and a PD 83 B for receiving the detection light reflected by the body.
  • the blood vessel simulation sensor 150 is accommodated in the device main body 222 in such a state that the sensitivity axis virtually coincides with the peripheral direction of the body (direction of the fingertips).
  • a case of using the first rigid type of blood vessel simulation sensor 150 as a body motion sensor was described above as an example, but it is also possible to use the second rigid type of blood vessel simulation sensor, the first elastic type of blood vessel simulation sensor 170 , the second resilient type of blood vessel simulation sensor 180 , or the acceleration sensor 210 as a blood vessel simulation sensor for the body motion sensor instead of the first rigid type of blood vessel simulation sensor 150 . Also in such cases, finger movements and other such small movements are not erroneously detected, the size of the sensor module is reduced, mounting is made easier, and the user's sensation of wearing the device is improved by incorporating the sensor used as the body motion sensor into the main body of the device.
  • a pulse measurement device 230 according to a sixth embodiment of the present invention will now be described with reference to FIGS. 112 and 113.
  • the main difference between the fourth embodiment and the sixth embodiment is that in the fourth embodiment, the sensor module 191 and the device main body 192 are provided separately and are connected by wiring, while in the sixth embodiment, the sensor module is incorporated into the main body of the device. Otherwise the basic configuration is similar to the fourth embodiment; therefore, in view of the similarity between the fourth embodiment and the sixth embodiment, descriptions of the parts of the sixth embodiment with identical or similar functions to the parts of the fourth embodiment may be omitted for the sake of simplicity.
  • FIG. 112 is an external perspective view of a case in which the pulse measurement device 230 of the sixth embodiment is incorporated in a watchcase.
  • FIG. 113 is a cross-sectional view of the pulse measurement device 230 in FIG. 112.
  • the pulse wave sensor 83 and a blood vessel simulation sensor 232 are provided on the reverse surface of a watchcase 231 .
  • the pulse wave sensor unit 83 described above is formed integrally with the main body on the reverse side of the watchcase 231 .
  • the watchcase 231 is provided with a wristband 233 for mounting the watchcase 231 on the arm, and the reverse side of the watchcase 231 is pressed against the back of the wrist when the wristband 233 is wound around the wrist.
  • the transparent glass 83 C constituting the pulse wave sensor 83 is fixed to the reverse side of the watchcase 231 by a back lid 234 .
  • the transparent glass 83 C transmits the light cast on the LED 83 A, transmits reflected light obtained via the body, and directs the light to the PD 83 B.
  • the front side of the watchcase 231 is provided with a liquid crystal display device or another such display device 97 for displaying the pulse rate HR and other such living organism information based on the detection results from the pulse wave sensor 83 in addition to the current time and date.
  • the interior of the watchcase 231 has a CPU and other such IC circuits on a main board 236 , whereby a data processing circuit 237 is configured.
  • the reverse side of the main board 236 is provided with a battery 238 , and the battery 238 supplies power to the display device 97 , the main board 236 , the pulse wave sensor 83 , and the blood vessel simulation sensor 232 .
  • the main board 236 and the pulse wave sensor 83 are connected by a heat seal 239 , power is supplied from the main board 236 to the pulse wave sensor 83 through a wiring formed by the heat seal 239 , and a pulse wave detection signal is fed from the pulse wave sensor 83 to the main board 236 .
  • the data processing circuit 237 subjects the pulse wave signal to FFT processing, and the pulse rate HR is calculated by analyzing the processing results.
  • the external surface of the watchcase 231 is provided with button switches (not shown) for time setting, display mode switching, and the like.
  • the reverse side of the watchcase 231 faces the back of the wrist when the wristband 233 is wound around the wrist. Therefore, the light from the LED 83 A is directed to the back of the wrist via the transparent glass 83 C, and the reflected light is received by the photo diode 83 B.
  • a case of using the blood vessel simulation sensor 232 as a body motion sensor was described above as an example, but it is also possible to use the first rigid type of blood vessel simulation sensor 150 , a second rigid type of blood vessel simulation sensor, the first resilient type of blood vessel simulation sensor 170 , the second resilient type of blood vessel simulation sensor 180 , or the acceleration sensor 210 as a blood vessel simulation sensor for the body motion sensor instead of the blood vessel simulation sensor 232 . Also in such cases, finger movements and other such small movements are not erroneously detected and mounting is made easier by incorporating the sensor used as the body motion sensor into the main body of the device.

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Cited By (46)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060122521A1 (en) * 2004-12-07 2006-06-08 Yu-Yu Chen Electronic wristwatch-type exercise signal detecting apparatus
US20070142730A1 (en) * 2005-12-13 2007-06-21 Franz Laermer Apparatus for noninvasive blood pressure measurement
US20110125037A1 (en) * 2009-11-20 2011-05-26 Seiko Epson Corporation Device for measuring biological information
US20120088982A1 (en) * 2010-07-28 2012-04-12 Impact Sports Technologies, Inc. Monitoring Device With An Accelerometer, Method And System
US20120203080A1 (en) * 2009-11-17 2012-08-09 Min-Joon Kim Photoplethysmography apparatus
US20120245472A1 (en) * 2010-07-28 2012-09-27 Impact Sports Technologies, Inc. Monitoring Device With An Accelerometer, Method And System
US20130178754A1 (en) * 2010-07-28 2013-07-11 Impact Sports Technologies, Inc. Monitoring Device With An Accelerometer, Method And System
US20130190629A1 (en) * 2012-01-25 2013-07-25 Shota Umeda Electronic sphygmomanometer for measuring blood pressure and pulse
US8579827B1 (en) * 2004-09-28 2013-11-12 Impact Sports Technologies, Inc. Monitoring device with an accelerometer, method and system
US20140350356A1 (en) * 2012-09-04 2014-11-27 Whoop Inc. Determining heart rate with reflected light data
US9155504B1 (en) * 2010-07-28 2015-10-13 Impact Sports Technologies, Inc. Method and system for monitoring a prisoner
US20160098081A1 (en) * 2014-10-01 2016-04-07 Seiko Epson Corporation Activity state information detecting device and method for controlling activity state information detecting device
US20160113589A1 (en) * 2014-10-23 2016-04-28 Samsung Electronics Co., Ltd. Biosignal processing method and apparatus
US9402551B2 (en) 2011-02-23 2016-08-02 Seiko Epson Corporation Pulse detector with unworn-state detection
US20160220122A1 (en) * 2015-01-25 2016-08-04 Aliphcom Physiological characteristics determinator
US20170007166A1 (en) * 2014-02-26 2017-01-12 Koninklijke Philips N.V. Device for measuring a cycling cadence
US9591973B1 (en) 2011-06-13 2017-03-14 Impact Sports Technologies, Inc. Monitoring device with a pedometer
US9629562B1 (en) 2014-07-25 2017-04-25 Impact Sports Technologies, Inc. Mobile plethysmographic device
US9675320B2 (en) 2012-03-26 2017-06-13 Hitachi, Ltd. Diagnostic ultrasound apparatus
JP2017519548A (ja) * 2014-05-28 2017-07-20 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． マルチチャネルｐｐｇ信号を使用するモーションアーチファクト低減
US9770176B2 (en) 2011-09-16 2017-09-26 Koninklijke Philips N.V. Device and method for estimating the heart rate during motion
US9788794B2 (en) 2014-02-28 2017-10-17 Valencell, Inc. Method and apparatus for generating assessments using physical activity and biometric parameters
US9808204B2 (en) 2007-10-25 2017-11-07 Valencell, Inc. Noninvasive physiological analysis using excitation-sensor modules and related devices and methods
US20180055450A1 (en) * 2011-01-27 2018-03-01 Valencell, Inc. Wearable monitoring device
US9955919B2 (en) 2009-02-25 2018-05-01 Valencell, Inc. Light-guiding devices and monitoring devices incorporating same
US9993204B2 (en) 2013-01-09 2018-06-12 Valencell, Inc. Cadence detection based on inertial harmonics
US10076282B2 (en) 2009-02-25 2018-09-18 Valencell, Inc. Wearable monitoring devices having sensors and light guides
US10258243B2 (en) 2006-12-19 2019-04-16 Valencell, Inc. Apparatus, systems, and methods for measuring environmental exposure and physiological response thereto
US10349847B2 (en) 2015-01-15 2019-07-16 Samsung Electronics Co., Ltd. Apparatus for detecting bio-information
US10349844B2 (en) 2012-01-16 2019-07-16 Valencell, Inc. Reduction of physiological metric error due to inertial cadence
US10357165B2 (en) 2015-09-01 2019-07-23 Samsung Electronics Co., Ltd. Method and apparatus for acquiring bioinformation and apparatus for testing bioinformation
US10390762B2 (en) 2012-01-16 2019-08-27 Valencell, Inc. Physiological metric estimation rise and fall limiting
US10405806B2 (en) 2015-03-06 2019-09-10 Samsung Electronics Co., Ltd. Apparatus for and method of measuring blood pressure
US10413197B2 (en) 2006-12-19 2019-09-17 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US20190307328A1 (en) * 2006-06-30 2019-10-10 Empire Ip Llc Personal Emergency Response (PER) System
US10512403B2 (en) 2011-08-02 2019-12-24 Valencell, Inc. Systems and methods for variable filter adjustment by heart rate metric feedback
US10568527B2 (en) 2014-09-03 2020-02-25 Samsung Electronics Co., Ltd. Apparatus for and method of monitoring blood pressure and wearable device having function of monitoring blood pressure
US10610158B2 (en) 2015-10-23 2020-04-07 Valencell, Inc. Physiological monitoring devices and methods that identify subject activity type
US10820858B2 (en) 2016-10-12 2020-11-03 Samsung Electronics Co., Ltd. Apparatus and method for estimating biometric information
US20200359919A1 (en) * 2014-08-07 2020-11-19 Apple Inc. Motion Artifact Removal by Time Domain Projection
US10945618B2 (en) 2015-10-23 2021-03-16 Valencell, Inc. Physiological monitoring devices and methods for noise reduction in physiological signals based on subject activity type
US10966662B2 (en) 2016-07-08 2021-04-06 Valencell, Inc. Motion-dependent averaging for physiological metric estimating systems and methods
US11109804B2 (en) 2014-11-19 2021-09-07 Amer Sports Digital Services Oy Wearable sports monitoring equipment and method for characterizing sports performances or sportspersons
US20210307692A1 (en) * 2017-07-25 2021-10-07 Samsung Electronics Co., Ltd. Apparatus and method for measuring biometric information
US11185241B2 (en) 2014-03-05 2021-11-30 Whoop, Inc. Continuous heart rate monitoring and interpretation
US11941182B2 (en) 2020-09-29 2024-03-26 Nintendo Co., Ltd. Electronic apparatus

Families Citing this family (35)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU2006325153B2 (en) * 2005-11-29 2013-03-28 PhysIQ Inc. Residual-based monitoring of human health
JP5042052B2 (ja) * 2007-09-25 2012-10-03 セイコーインスツル株式会社 電子歩数計
JP5369726B2 (ja) * 2009-02-02 2013-12-18 セイコーエプソン株式会社 拍動検出装置、および拍動検出方法
US9750462B2 (en) 2009-02-25 2017-09-05 Valencell, Inc. Monitoring apparatus and methods for measuring physiological and/or environmental conditions
EP3142071A1 (en) * 2009-10-06 2017-03-15 Koninklijke Philips N.V. Method and system for obtaining a first signal for analysis to characterize at least one periodic component thereof
WO2012073069A1 (en) * 2010-11-30 2012-06-07 Spo Medical Equipment Ltd. A method and system for pulse measurement
CN102551685B (zh) * 2010-12-30 2015-04-01 世意法（北京）半导体研发有限责任公司 对象监视器
US9427191B2 (en) 2011-07-25 2016-08-30 Valencell, Inc. Apparatus and methods for estimating time-state physiological parameters
WO2013054477A1 (ja) 2011-10-11 2013-04-18 株式会社村田製作所 携帯機器
JP5998563B2 (ja) * 2012-03-27 2016-09-28 セイコーエプソン株式会社 拍動検出装置、電子機器及びプログラム
CN108937908B (zh) 2013-01-28 2021-08-10 瓦伦赛尔公司 具有与身体运动脱开的感测元件的生理监测装置
JP5979604B2 (ja) * 2013-02-06 2016-08-24 カシオ計算機株式会社 生体情報検出装置及び生体情報検出方法、生体情報検出プログラム
CN103505195B (zh) * 2013-09-02 2015-06-17 展讯通信（上海）有限公司 人体脉搏测量方法、装置和移动终端
KR102215442B1 (ko) 2013-11-26 2021-02-15 삼성전자주식회사 착용형 모바일 기기, 및 착용형 모바일 기기의 생체신호의 선택적 활용 방법
JP5880535B2 (ja) * 2013-12-25 2016-03-09 セイコーエプソン株式会社 生体情報検出装置
JP5895993B2 (ja) * 2013-12-25 2016-03-30 セイコーエプソン株式会社 生体情報測定機器
WO2015107269A1 (en) * 2014-01-16 2015-07-23 Medieta Oy Device and method for measuring arterial signals
CN103932688B (zh) * 2014-05-15 2016-01-13 成都天奥电子股份有限公司 猝死预警装置及应用猝死预警装置的手表
US20160029898A1 (en) 2014-07-30 2016-02-04 Valencell, Inc. Physiological Monitoring Devices and Methods Using Optical Sensors
WO2016022295A1 (en) 2014-08-06 2016-02-11 Valencell, Inc. Optical physiological sensor modules with reduced signal noise
US9794653B2 (en) 2014-09-27 2017-10-17 Valencell, Inc. Methods and apparatus for improving signal quality in wearable biometric monitoring devices
JP6226088B2 (ja) * 2014-12-05 2017-11-08 株式会社村田製作所 疲労検出装置
JP6491920B2 (ja) * 2015-03-25 2019-03-27 クリムゾンテクノロジー株式会社 生体信号処理装置及び生体信号処理方法
JP6597083B2 (ja) * 2015-09-07 2019-10-30 オムロンヘルスケア株式会社 脈波検出装置
JP2017051554A (ja) * 2015-09-11 2017-03-16 株式会社東芝 脈波計測装置、脈波計測システム、および信号処理方法
JP6197926B2 (ja) * 2016-08-01 2017-09-20 カシオ計算機株式会社 生体情報検出装置及び生体情報検出方法、生体情報検出プログラム
JP6723132B2 (ja) * 2016-09-29 2020-07-15 ルネサスエレクトロニクス株式会社 脈拍測定装置、光量制御方法、及びプログラム
US10722125B2 (en) * 2016-10-31 2020-07-28 Livemetric (Medical) S.A. Blood pressure signal acquisition using a pressure sensor array
US20180353090A1 (en) * 2017-06-13 2018-12-13 Huami Inc. Adaptive Heart Rate Estimation
CN109171685B (zh) * 2018-09-20 2021-10-08 芯海科技（深圳）股份有限公司 模拟人体生理信号的方法、设备及存储介质
CN109875541A (zh) * 2018-12-28 2019-06-14 北京津发科技股份有限公司 脉搏测量方法、脉搏测量装置及存储介质
CN109864731B (zh) * 2018-12-28 2022-07-01 北京津发科技股份有限公司 一种脉搏测量方法和装置及终端设备、可读存储介质
CN112205971B (zh) * 2020-09-17 2022-06-21 四川长虹电器股份有限公司 一种非接触式脉搏波波速测量装置
CN114431841A (zh) * 2020-10-30 2022-05-06 深圳市云中飞电子有限公司 一种脉搏信号检测方法、可穿戴设备及存储介质
CN114209308B (zh) * 2021-11-23 2023-10-13 湖南云医链生物科技有限公司 中医生命活力的衡量方法、装置、设备及存储介质

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4832484A (en) * 1986-10-29 1989-05-23 Nihon Kohden Corporation Apparatus for determining the concentration of a light-absorbing material in blood
US6081742A (en) * 1996-09-10 2000-06-27 Seiko Epson Corporation Organism state measuring device and relaxation instructing device
US6699199B2 (en) * 2000-04-18 2004-03-02 Massachusetts Institute Of Technology Photoplethysmograph signal-to-noise line enhancement
US7018338B2 (en) * 2001-09-28 2006-03-28 Csem Centre Suisse D'electronique Et De Microtechnique Sa Method and device for pulse rate detection

Family Cites Families (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5542421A (en) * 1992-07-31 1996-08-06 Frederick Erdman Association Method and apparatus for cardiovascular diagnosis
JP3417006B2 (ja) 1993-10-26 2003-06-16 セイコーエプソン株式会社 ピッチメーカ
JP2816944B2 (ja) 1993-12-20 1998-10-27 セイコーインスツルメンツ株式会社 脈拍計
JP3301294B2 (ja) 1995-09-13 2002-07-15 セイコーエプソン株式会社 健康状態管理装置
JP3036954U (ja) 1996-09-21 1997-05-06 株式会社ジー・エム・エス 携帯用心拍間隔記録装置
DE19757974A1 (de) * 1997-12-24 1999-07-15 Braun Gmbh Verfahren und Meßgerät zur Bestimmung des Blutdrucks
JPH11276448A (ja) 1998-03-31 1999-10-12 Seiko Epson Corp 信号抽出装置および信号抽出方法
JP2000051164A (ja) 1998-08-07 2000-02-22 Seiko Instruments Inc 脈波検出装置
JP2000308639A (ja) 1999-04-28 2000-11-07 Seiko Instruments Inc 脈波検出装置
JP2003511101A (ja) * 1999-10-07 2003-03-25 ミルズ，アレクサンダー，ケイ． 生理学的特性の非侵襲的連続決定装置および方法
DE19963633A1 (de) * 1999-12-29 2001-07-12 Braun Gmbh Blutdruckmeßgerät mit Neigungssensor
JP2001275998A (ja) 2000-03-30 2001-10-09 Mitsuba Corp 血圧測定方法および血圧測定装置
US6819950B2 (en) * 2000-10-06 2004-11-16 Alexander K. Mills Method for noninvasive continuous determination of physiologic characteristics
JP2002224061A (ja) 2001-01-31 2002-08-13 Omron Corp 電子血圧計
JP2003250771A (ja) 2002-03-04 2003-09-09 Sousei Denshi:Kk 血圧測定装置および血圧値への換算方法
US7674231B2 (en) * 2005-08-22 2010-03-09 Massachusetts Institute Of Technology Wearable pulse wave velocity blood pressure sensor and methods of calibration thereof

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4832484A (en) * 1986-10-29 1989-05-23 Nihon Kohden Corporation Apparatus for determining the concentration of a light-absorbing material in blood
US6081742A (en) * 1996-09-10 2000-06-27 Seiko Epson Corporation Organism state measuring device and relaxation instructing device
US6699199B2 (en) * 2000-04-18 2004-03-02 Massachusetts Institute Of Technology Photoplethysmograph signal-to-noise line enhancement
US7018338B2 (en) * 2001-09-28 2006-03-28 Csem Centre Suisse D'electronique Et De Microtechnique Sa Method and device for pulse rate detection

Cited By (102)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9226669B1 (en) * 2004-09-28 2016-01-05 Impact Sports Technologies, Inc. Optical sensor for a monitoring device
US8579827B1 (en) * 2004-09-28 2013-11-12 Impact Sports Technologies, Inc. Monitoring device with an accelerometer, method and system
US20060122521A1 (en) * 2004-12-07 2006-06-08 Yu-Yu Chen Electronic wristwatch-type exercise signal detecting apparatus
US20070142730A1 (en) * 2005-12-13 2007-06-21 Franz Laermer Apparatus for noninvasive blood pressure measurement
US11877821B2 (en) * 2006-06-30 2024-01-23 Bt Wearables Llc Personal monitoring apparatus
US20190307328A1 (en) * 2006-06-30 2019-10-10 Empire Ip Llc Personal Emergency Response (PER) System
US11109767B2 (en) 2006-12-19 2021-09-07 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US10716481B2 (en) 2006-12-19 2020-07-21 Valencell, Inc. Apparatus, systems and methods for monitoring and evaluating cardiopulmonary functioning
US11000190B2 (en) 2006-12-19 2021-05-11 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US10987005B2 (en) 2006-12-19 2021-04-27 Valencell, Inc. Systems and methods for presenting personal health information
US11350831B2 (en) 2006-12-19 2022-06-07 Valencell, Inc. Physiological monitoring apparatus
US10258243B2 (en) 2006-12-19 2019-04-16 Valencell, Inc. Apparatus, systems, and methods for measuring environmental exposure and physiological response thereto
US11272848B2 (en) 2006-12-19 2022-03-15 Valencell, Inc. Wearable apparatus for multiple types of physiological and/or environmental monitoring
US10413197B2 (en) 2006-12-19 2019-09-17 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US11272849B2 (en) 2006-12-19 2022-03-15 Valencell, Inc. Wearable apparatus
US11083378B2 (en) 2006-12-19 2021-08-10 Valencell, Inc. Wearable apparatus having integrated physiological and/or environmental sensors
US11295856B2 (en) 2006-12-19 2022-04-05 Valencell, Inc. Apparatus, systems, and methods for measuring environmental exposure and physiological response thereto
US11324407B2 (en) 2006-12-19 2022-05-10 Valencell, Inc. Methods and apparatus for physiological and environmental monitoring with optical and footstep sensors
US11412938B2 (en) 2006-12-19 2022-08-16 Valencell, Inc. Physiological monitoring apparatus and networks
US11399724B2 (en) 2006-12-19 2022-08-02 Valencell, Inc. Earpiece monitor
US10595730B2 (en) 2006-12-19 2020-03-24 Valencell, Inc. Physiological monitoring methods
US11395595B2 (en) 2006-12-19 2022-07-26 Valencell, Inc. Apparatus, systems and methods for monitoring and evaluating cardiopulmonary functioning
US9808204B2 (en) 2007-10-25 2017-11-07 Valencell, Inc. Noninvasive physiological analysis using excitation-sensor modules and related devices and methods
US11589812B2 (en) 2009-02-25 2023-02-28 Valencell, Inc. Wearable devices for physiological monitoring
US10448840B2 (en) 2009-02-25 2019-10-22 Valencell, Inc. Apparatus for generating data output containing physiological and motion-related information
US10716480B2 (en) 2009-02-25 2020-07-21 Valencell, Inc. Hearing aid earpiece covers
US10750954B2 (en) 2009-02-25 2020-08-25 Valencell, Inc. Wearable devices with flexible optical emitters and/or optical detectors
US10842389B2 (en) 2009-02-25 2020-11-24 Valencell, Inc. Wearable audio devices
US10542893B2 (en) 2009-02-25 2020-01-28 Valencell, Inc. Form-fitted monitoring apparatus for health and environmental monitoring
US10842387B2 (en) 2009-02-25 2020-11-24 Valencell, Inc. Apparatus for assessing physiological conditions
US11471103B2 (en) 2009-02-25 2022-10-18 Valencell, Inc. Ear-worn devices for physiological monitoring
US9955919B2 (en) 2009-02-25 2018-05-01 Valencell, Inc. Light-guiding devices and monitoring devices incorporating same
US10898083B2 (en) * 2009-02-25 2021-01-26 Valencell, Inc. Wearable monitoring devices with passive and active filtering
US10076282B2 (en) 2009-02-25 2018-09-18 Valencell, Inc. Wearable monitoring devices having sensors and light guides
US10092245B2 (en) 2009-02-25 2018-10-09 Valencell, Inc. Methods and apparatus for detecting motion noise and for removing motion noise from physiological signals
US10973415B2 (en) 2009-02-25 2021-04-13 Valencell, Inc. Form-fitted monitoring apparatus for health and environmental monitoring
US11026588B2 (en) 2009-02-25 2021-06-08 Valencell, Inc. Methods and apparatus for detecting motion noise and for removing motion noise from physiological signals
US11160460B2 (en) 2009-02-25 2021-11-02 Valencell, Inc. Physiological monitoring methods
US11660006B2 (en) 2009-02-25 2023-05-30 Valencell, Inc. Wearable monitoring devices with passive and active filtering
US20120203080A1 (en) * 2009-11-17 2012-08-09 Min-Joon Kim Photoplethysmography apparatus
US9282903B2 (en) 2009-11-20 2016-03-15 Seiko Epson Corporation Device for measuring biological information
US20110125037A1 (en) * 2009-11-20 2011-05-26 Seiko Epson Corporation Device for measuring biological information
US20120088982A1 (en) * 2010-07-28 2012-04-12 Impact Sports Technologies, Inc. Monitoring Device With An Accelerometer, Method And System
US9155504B1 (en) * 2010-07-28 2015-10-13 Impact Sports Technologies, Inc. Method and system for monitoring a prisoner
US20120245472A1 (en) * 2010-07-28 2012-09-27 Impact Sports Technologies, Inc. Monitoring Device With An Accelerometer, Method And System
US8460199B2 (en) * 2010-07-28 2013-06-11 Impact Sports Technologies, Inc. Monitoring device with an accelerometer, method and system
US9039627B2 (en) * 2010-07-28 2015-05-26 Impact Sports Technologies, Inc. Monitoring device with an accelerometer, method and system
US20130178754A1 (en) * 2010-07-28 2013-07-11 Impact Sports Technologies, Inc. Monitoring Device With An Accelerometer, Method And System
US10827979B2 (en) 2011-01-27 2020-11-10 Valencell, Inc. Wearable monitoring device
US20180055450A1 (en) * 2011-01-27 2018-03-01 Valencell, Inc. Wearable monitoring device
US11324445B2 (en) 2011-01-27 2022-05-10 Valencell, Inc. Headsets with angled sensor modules
US9402551B2 (en) 2011-02-23 2016-08-02 Seiko Epson Corporation Pulse detector with unworn-state detection
US9820659B1 (en) 2011-06-13 2017-11-21 Impact Sports Technologies, Inc. Monitoring device with a pedometer
US9591973B1 (en) 2011-06-13 2017-03-14 Impact Sports Technologies, Inc. Monitoring device with a pedometer
US10512403B2 (en) 2011-08-02 2019-12-24 Valencell, Inc. Systems and methods for variable filter adjustment by heart rate metric feedback
US11375902B2 (en) 2011-08-02 2022-07-05 Valencell, Inc. Systems and methods for variable filter adjustment by heart rate metric feedback
US9770176B2 (en) 2011-09-16 2017-09-26 Koninklijke Philips N.V. Device and method for estimating the heart rate during motion
US10617308B2 (en) 2011-09-16 2020-04-14 Koninklijke Philips N.V. Device and method for estimating the heart rate during motion
US10631740B2 (en) 2012-01-16 2020-04-28 Valencell, Inc. Reduction of physiological metric error due to inertial cadence
US11350884B2 (en) 2012-01-16 2022-06-07 Valencell, Inc. Physiological metric estimation rise and fall limiting
US10349844B2 (en) 2012-01-16 2019-07-16 Valencell, Inc. Reduction of physiological metric error due to inertial cadence
US10390762B2 (en) 2012-01-16 2019-08-27 Valencell, Inc. Physiological metric estimation rise and fall limiting
US10542896B2 (en) 2012-01-16 2020-01-28 Valencell, Inc. Reduction of physiological metric error due to inertial cadence
US20130190629A1 (en) * 2012-01-25 2013-07-25 Shota Umeda Electronic sphygmomanometer for measuring blood pressure and pulse
US10390710B2 (en) * 2012-01-25 2019-08-27 Omron Healthcare Co., Ltd. Electronic sphygmomanometer for measuring blood pressure and pulse
US9675320B2 (en) 2012-03-26 2017-06-13 Hitachi, Ltd. Diagnostic ultrasound apparatus
US11410765B2 (en) 2012-09-04 2022-08-09 Whoop, Inc. Continuously wearable monitoring device
US20140350356A1 (en) * 2012-09-04 2014-11-27 Whoop Inc. Determining heart rate with reflected light data
US10264982B2 (en) 2012-09-04 2019-04-23 Whoop, Inc. Physiological measurement system with motion sensing
US11602279B2 (en) 2012-09-04 2023-03-14 Whoop, Inc. Automated exercise recommendations
US9993204B2 (en) 2013-01-09 2018-06-12 Valencell, Inc. Cadence detection based on inertial harmonics
US11363987B2 (en) 2013-01-09 2022-06-21 Valencell, Inc. Cadence detection based on inertial harmonics
US20170007166A1 (en) * 2014-02-26 2017-01-12 Koninklijke Philips N.V. Device for measuring a cycling cadence
US9936912B2 (en) * 2014-02-26 2018-04-10 Koninklijke Philips N.V. Device for measuring a cycling cadence
US10413250B2 (en) 2014-02-28 2019-09-17 Valencell, Inc. Method and apparatus for generating assessments using physical activity and biometric parameters
US10206627B2 (en) 2014-02-28 2019-02-19 Valencell, Inc. Method and apparatus for generating assessments using physical activity and biometric parameters
US9788794B2 (en) 2014-02-28 2017-10-17 Valencell, Inc. Method and apparatus for generating assessments using physical activity and biometric parameters
US11298036B2 (en) 2014-02-28 2022-04-12 Valencell, Inc. Wearable device including PPG and inertial sensors for assessing physical activity and biometric parameters
US10856813B2 (en) 2014-02-28 2020-12-08 Valencell, Inc. Method and apparatus for generating assessments using physical activity and biometric parameters
US11185241B2 (en) 2014-03-05 2021-11-30 Whoop, Inc. Continuous heart rate monitoring and interpretation
US10398383B2 (en) 2014-05-28 2019-09-03 Koninklijke Philips N.V. Motion artifact reduction using multi-channel PPG signals
US11219414B2 (en) 2014-05-28 2022-01-11 Koninklijke Philips N.V. Motion artifact reduction using multi-channel PPG signals
JP2017519548A (ja) * 2014-05-28 2017-07-20 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． マルチチャネルｐｐｇ信号を使用するモーションアーチファクト低減
US9629562B1 (en) 2014-07-25 2017-04-25 Impact Sports Technologies, Inc. Mobile plethysmographic device
US20200359919A1 (en) * 2014-08-07 2020-11-19 Apple Inc. Motion Artifact Removal by Time Domain Projection
US10568527B2 (en) 2014-09-03 2020-02-25 Samsung Electronics Co., Ltd. Apparatus for and method of monitoring blood pressure and wearable device having function of monitoring blood pressure
US20160098081A1 (en) * 2014-10-01 2016-04-07 Seiko Epson Corporation Activity state information detecting device and method for controlling activity state information detecting device
US9877683B2 (en) * 2014-10-01 2018-01-30 Seiko Epson Corporation Activity state information detecting device and method for controlling activity state information detecting device
US20160113589A1 (en) * 2014-10-23 2016-04-28 Samsung Electronics Co., Ltd. Biosignal processing method and apparatus
US11766214B2 (en) 2014-11-19 2023-09-26 Suunto Oy Wearable sports monitoring equipment and method for characterizing sports performances or sportspersons
US11109804B2 (en) 2014-11-19 2021-09-07 Amer Sports Digital Services Oy Wearable sports monitoring equipment and method for characterizing sports performances or sportspersons
US10349847B2 (en) 2015-01-15 2019-07-16 Samsung Electronics Co., Ltd. Apparatus for detecting bio-information
US20160220122A1 (en) * 2015-01-25 2016-08-04 Aliphcom Physiological characteristics determinator
US10405806B2 (en) 2015-03-06 2019-09-10 Samsung Electronics Co., Ltd. Apparatus for and method of measuring blood pressure
US10357165B2 (en) 2015-09-01 2019-07-23 Samsung Electronics Co., Ltd. Method and apparatus for acquiring bioinformation and apparatus for testing bioinformation
US10945618B2 (en) 2015-10-23 2021-03-16 Valencell, Inc. Physiological monitoring devices and methods for noise reduction in physiological signals based on subject activity type
US10610158B2 (en) 2015-10-23 2020-04-07 Valencell, Inc. Physiological monitoring devices and methods that identify subject activity type
US10966662B2 (en) 2016-07-08 2021-04-06 Valencell, Inc. Motion-dependent averaging for physiological metric estimating systems and methods
US11666277B2 (en) 2016-10-12 2023-06-06 Samsung Electronics Co., Ltd. Apparatus and method for estimating biometric information
US10820858B2 (en) 2016-10-12 2020-11-03 Samsung Electronics Co., Ltd. Apparatus and method for estimating biometric information
US20210307692A1 (en) * 2017-07-25 2021-10-07 Samsung Electronics Co., Ltd. Apparatus and method for measuring biometric information
US11941182B2 (en) 2020-09-29 2024-03-26 Nintendo Co., Ltd. Electronic apparatus

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