WO2017199945A1 - 呼吸波形描画システム及び生体情報モニタリングシステム - Google Patents

呼吸波形描画システム及び生体情報モニタリングシステム Download PDF

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Publication number
WO2017199945A1
WO2017199945A1 PCT/JP2017/018338 JP2017018338W WO2017199945A1 WO 2017199945 A1 WO2017199945 A1 WO 2017199945A1 JP 2017018338 W JP2017018338 W JP 2017018338W WO 2017199945 A1 WO2017199945 A1 WO 2017199945A1
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Prior art keywords
subject
waveform
vibration
load
bed
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Ceased
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PCT/JP2017/018338
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English (en)
French (fr)
Japanese (ja)
Inventor
浩之 赤津
徳仁 飯田
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MinebeaMitsumi Inc
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MinebeaMitsumi Inc
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Priority to EP17799369.8A priority Critical patent/EP3459452B1/en
Priority to CN201780043419.7A priority patent/CN109475324B/zh
Publication of WO2017199945A1 publication Critical patent/WO2017199945A1/ja
Priority to US16/191,922 priority patent/US10758187B2/en
Anticipated expiration legal-status Critical
Ceased 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
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/0816—Measuring devices for examining respiratory frequency
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring 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 or mobility of a limb
    • A61B5/1102—Ballistocardiography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring 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 or mobility of a limb
    • A61B5/1113—Local tracking of patients, e.g. in a hospital or private home
    • A61B5/1115—Monitoring leaving of a patient support, e.g. a bed or a wheelchair
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring 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 or mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor or mobility of a limb occurring during breathing
    • 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
    • A61B5/6887—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient mounted on external non-worn devices, e.g. non-medical devices
    • A61B5/6892—Mats
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61G—TRANSPORT, PERSONAL CONVEYANCES, OR ACCOMMODATION SPECIALLY ADAPTED FOR PATIENTS OR DISABLED PERSONS; OPERATING TABLES OR CHAIRS; CHAIRS FOR DENTISTRY; FUNERAL DEVICES
    • A61G7/00—Beds specially adapted for nursing; Devices for lifting patients or disabled persons
    • A61G7/05—Parts, details or accessories of beds
    • 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
    • A61B2562/0252—Load cells
    • 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
    • A61B2562/04—Arrangements of multiple sensors of the same type
    • A61B2562/046—Arrangements of multiple sensors of the same type in a matrix array
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/0803—Recording apparatus specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring 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 or mobility of a limb
    • A61B5/1121—Determining geometric values, e.g. centre of rotation or angular range of movement
    • 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
    • A61B5/6887—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient mounted on external non-worn devices, e.g. non-medical devices
    • A61B5/6891—Furniture

Definitions

  • the present invention relates to a respiratory waveform drawing system that draws a respiratory waveform of a subject based on a change in the position of the center of gravity of the subject, and a biological information monitoring system that monitors the biological information of the subject based on a change in the position of the center of gravity of the subject.
  • the biological information of the subject is one of important information for knowing the physical condition of the patient and the cared person in the medical or nursing care field. For example, it is possible to grasp the respiratory state of the subject, to grasp symptoms such as sleep apnea syndrome and snoring, and to improve these symptoms.
  • Patent Document 1 It has been proposed to place a load sensor under the leg of the bed and measure the breathing state of the subject based on the measurement value of the load sensor (Patent Document 1). Furthermore, a load detector is arranged under the leg of the bed to determine the movement of the center of gravity of the test organism on the bed, and based on the movement of the center of gravity, the respiratory motion and heartbeat motion of the test organism can be determined. It has been proposed (Patent Document 2).
  • an object of the present invention is to provide a respiration waveform drawing system and a respiration waveform drawing method capable of presenting a waveform indicating respiration of a subject almost in real time.
  • a respiratory waveform drawing system for drawing a respiratory waveform of a subject on a bed, A plurality of load detectors that are provided under the bed or under the legs of the bed and detect the load of the subject and output as a load signal; A subject number determination unit for determining the number of subjects on the bed based on the frequency spectrum of the load signal; When it is determined that the number of subjects on the bed is plural, a waveform separation unit that separates the load components of each subject for each load signal output from each load detector; Based on the separated load component, a center-of-gravity position calculation unit that calculates the center-of-gravity position of each subject; A respiratory waveform drawing system is provided that includes a waveform drawing unit that draws a respiratory waveform of each subject based on temporal variation of the center of gravity position of each subject.
  • the subject number determination unit may determine the number of peak frequencies appearing in the frequency spectrum of the load signal as the number of subjects on the bed.
  • the respiratory waveform drawing system may further include a vibration coordinate setting unit that sets a vibration origin and a vibration axis of each subject's respiration waveform, and the vibration coordinate setting unit has a certain time for each subject.
  • the first extreme point that is the position where the distance between the initial center and the center of gravity displaced from the initial origin is the maximum is obtained using the center of gravity position at the initial origin, and is opposite to the first extreme point of the initial origin
  • a second extreme point which is a position where the distance between the center of gravity that appears on the side and is displaced from the first extreme point and the initial origin is maximum is obtained, and the first extreme point and the second extreme point May be set as the temporary vibration axis, and the midpoint of the first extreme value point and the second extreme value point may be set as the temporary vibration origin, and the waveform drawing unit is projected onto the temporary vibration axis.
  • the respiratory waveform drawing system may further include a drawing compensation unit that compensates a drawing state of each subject's respiratory waveform, and the drawing compensation unit predicts each subject based on a past respiratory waveform.
  • a prediction waveform generation unit that generates a waveform and a correction distance calculation unit that calculates a distance between the respiration waveform and the prediction waveform at a predetermined sampling time for each subject may be provided, and drawing of the respiration waveform of each subject The state may be compensated according to the distance.
  • a biological information monitoring system for monitoring biological information of a subject on a bed, A plurality of load detectors that are provided under the bed or under the legs of the bed and detect the load of the subject and output as a load signal; A subject number determination unit for determining the number of subjects on the bed based on the frequency spectrum of the load signal; When it is determined that the number of subjects on the bed is plural, a waveform separation unit that separates the load component of each subject for each load signal output from each load detector, The separated load component is provided with a biological information monitoring system that is used to monitor biological information of each subject.
  • the biological information monitoring system may monitor a waveform representing the heartbeat of each subject as the biological information of each subject.
  • the respiratory waveform drawing system and the respiratory waveform drawing method of the present invention it is possible to present a waveform indicating the breathing of the subject almost in real time.
  • FIG. 1 is a block diagram showing a configuration of a biological information monitoring system according to an embodiment of the present invention.
  • FIG. 2 is a flowchart showing the center of gravity locus calculation method according to the embodiment of the present invention.
  • FIG. 3 is an explanatory diagram showing the arrangement of the load detector with respect to the bed.
  • FIG. 4 is an explanatory diagram showing the arrangement of four load detection areas defined on the upper surface of the bed.
  • FIG. 5 shows an example of a load signal from the load detector.
  • FIG. 6 shows an example of the subject's center of gravity locus.
  • FIG. 7 is a flowchart showing a waveform drawing method according to the embodiment of the present invention.
  • FIG. 8 shows another example of the subject's center of gravity locus.
  • FIG. 1 is a block diagram showing a configuration of a biological information monitoring system according to an embodiment of the present invention.
  • FIG. 2 is a flowchart showing the center of gravity locus calculation method according to the embodiment of the present invention.
  • FIG. 9A is an enlarged view of the center of gravity locus shown in FIG.
  • FIG. 9B is an enlarged view of the center of gravity locus shown in FIG.
  • FIG. 9C is an enlarged view of the center of gravity locus shown in FIG.
  • FIG. 10 is a flowchart showing the procedure of the vibration coordinate setting process.
  • FIG. 11A is an explanatory diagram for explaining a method of determining the vibration origin and the vibration axis, and shows an example of the set first temporary vibration origin.
  • FIG. 11B shows a provisional respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG.
  • FIG. 12A is an explanatory diagram for explaining a method of determining the vibration origin and the vibration axis, and shows an example of the distance between the first temporary vibration origin and the center of gravity.
  • FIG. 12B shows a provisional respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG. Fig.13 (a) is explanatory drawing for demonstrating the determination method of a vibration origin and a vibration axis, and shows an example of the set 1st extreme value point.
  • FIG. 13B shows a state of a temporary respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG.
  • FIG. 14A is an explanatory diagram for explaining a method of determining the vibration origin and the vibration axis, and shows an example of the set first temporary vibration axis.
  • FIG. 14B shows a provisional respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG. FIG.
  • FIG. 15A is an explanatory diagram for explaining a method of determining the vibration origin and the vibration axis. The distance between the first provisional vibration origin and the leg of the perpendicular line drawn from the center of gravity to the first provisional vibration axis. An example is shown.
  • FIG. 15B shows a provisional respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG.
  • FIG. 16A is an explanatory diagram for explaining a method of determining the vibration origin and the vibration axis, and shows an example of the set second extreme value point.
  • FIG. 16B shows a state of a temporary respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG. FIG.
  • FIG. 17A is an explanatory diagram for explaining a method of determining the vibration origin and the vibration axis, and shows an example of the set second temporary vibration origin and the second temporary vibration axis.
  • FIG. 17B shows a provisional respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG.
  • FIG. 18A is an explanatory diagram for explaining a method of determining the vibration origin and the vibration axis, and shows an example of the set vibration origin and vibration axis.
  • FIG. 18B shows a provisional respiratory waveform drawn by the waveform drawing unit up to the time corresponding to FIG. FIG.
  • FIG. 19A is an explanatory diagram for explaining a method of drawing a respiration waveform using the determined vibration origin and vibration axis, and the vibration origin and a perpendicular foot drawn from the center of gravity to the vibration axis. An example of the distance is shown.
  • FIG. 19B shows the state of the temporary respiratory waveform and the normal respiratory waveform drawn in the waveform drawing unit up to the time corresponding to FIG.
  • FIG. 20 is a graph showing an example of the breathing waveform of the subject, and the respiratory waveform before the body motion and the breathing waveform after the body motion are in the vibration axis direction due to the shift of the center of gravity of the subject due to the body motion of the subject.
  • Fig. 2 shows a state where the drawing is shifted.
  • FIG. 21 is a block diagram illustrating a detailed configuration of the drawing compensation unit.
  • FIG. 22 is a flowchart showing the procedure of the drawing compensation process.
  • FIG. 23 is an explanatory diagram for explaining a drawing compensation method.
  • FIG. 24 is an example of a frequency spectrum in a frequency band corresponding to the frequency of respiration of the load signal.
  • FIG. 25 is an explanatory diagram for explaining another method of drawing compensation.
  • FIG. 26 shows an example of the frequency profile of the subject.
  • FIG. 27 is a block diagram illustrating an overall configuration of a bed system according to a modification.
  • the biological information monitoring system 100 performs observation and measurement in order to grasp the biological state of the subject on the bed, and detects the load.
  • Unit 1 control unit 3, storage unit 4, and display unit 5 are mainly included.
  • the load detection unit 1 and the control unit 3 are connected via an A / D conversion unit 2.
  • a notification unit 6 and an input unit 7 are connected to the control unit 3.
  • the load detector 1 includes four load detectors 11, 12, 13, and 14. Each of the load detectors 11, 12, 13, and 14 is a load detector that detects a load using, for example, a beam-type load cell. Such a load detector is described in, for example, Japanese Patent No. 4829020 and Japanese Patent No. 4002905. Each of the load detectors 11, 12, 13, and 14 is connected to the A / D converter 2 by wiring.
  • the four load detectors 11, 12, 13, and 14 of the load detection unit 1 are arranged under the legs of the bed used by the subject. Specifically, as shown in FIG. 3, the load detectors 11, 12, 13, and 14 are below the casters C 1 , C 2 , C 3 , and C 4 attached to the lower ends of the legs at the four corners of the bed BD. Each is arranged.
  • the A / D converter 2 includes an A / D converter that converts an analog signal from the load detector 1 into a digital signal, and is connected to the load detector 1 and the controller 3 by wiring.
  • the control unit 3 is a dedicated or general-purpose computer, and includes a center-of-gravity position calculation unit 31, a body motion detection unit (body motion determination unit) 32, a waveform separation unit (load separation unit) 33, a vibration coordinate setting unit 34, and a waveform.
  • a drawing unit 35 and a drawing compensation unit 36 are constructed.
  • the storage unit 4 is a storage device that stores data used in the biological information monitoring system 100.
  • a hard disk magnetic disk
  • the display unit 5 is a monitor such as a liquid crystal monitor that displays information output from the control unit 3 to a user of the biological information monitoring system 100.
  • the notification unit 6 includes a device that performs predetermined notification visually or audibly based on information from the control unit 3, for example, a speaker.
  • the input unit 7 is an interface for performing a predetermined input to the control unit 3 and can be a keyboard and a mouse.
  • a biological information monitoring system 100 it is possible to detect and monitor various biological information including the respiratory state of the subject on the bed. Acquisition and monitoring of various types of biological information are performed based on changes in the position of the center of gravity of the subject on the bed.
  • the calculation of the center of gravity position of the subject using the biological information monitoring system 100 includes a load detection step (S01) for detecting the load of the subject, and temporal variation of the center of gravity position of the subject based on the detected load. And a gravity center locus calculation step (S02) for calculating (center of gravity locus).
  • the load of the subject S on the bed BD is detected using the load detectors 11, 12, 13, and 14. Since the load detectors 11, 12, 13, and 14 are respectively disposed below the casters C 1 , C 2 , C 3 , and C 4 as described above, loads applied to the upper surface of the bed BD are four loads.
  • the detectors 11, 12, 13, and 14 are dispersed and detected. Specifically, as shown in FIG. 4, the rectangular upper surface of the bed BD is equally divided into four rectangular areas I to IV by being divided into two parts vertically and horizontally.
  • the load applied to the region I where the lower left half of the subject S lying on the bed BD is mainly detected by the load detector 11, and the lower right half of the subject S in the same state is detected.
  • the load applied to the region II where the is located is mainly detected by the load detector 12.
  • the load applied to the region III where the upper right half of the subject S lying on the bed BD is located is mainly detected by the load detector 13, and the region IV where the upper left half of the subject S in the same state is located.
  • the load applied to is mainly detected by the load detector 14.
  • the total output from the load detectors 11, 12, 13, and 14 represents the weight of the bed alone
  • the load Since the total output from the detectors 11, 12, 13, and 14 represents the weight of the bed alone and the weight of the subject S, the subject S can store the weight of the bed alone in the storage unit 4 in advance.
  • the weight of the subject S can be measured when he is in bed. If the weight of the bed is not uniform in the four areas, the difference is stored as the bed weight corresponding to the load detector.
  • the load detectors 11, 12, 13, and 14 each detect a load (load change) and output it to the A / D converter 2 as an analog signal.
  • the A / D conversion unit 2 converts the analog signal into a digital signal with a sampling period of, for example, 5 milliseconds, and outputs the digital signal to the control unit 3 as a digital signal (hereinafter “load signal”).
  • FIG. 5 shows load signals s 1 (solid line), s 2 (dashed line), and s 3 (dashed line) output from the load detectors 11, 12, 13, and 14 output from time t 10 to time t 14.
  • S 4 two-dot chain line.
  • the subject S lies on the center of the bed BD as shown in FIG. 4 from time t 10 to time t 11 (period P 11 ), and from time t 11 to time t 12 ( During the period P 12 ), the bed BD moves to the areas I and IV of the bed BD, and during the period from the time t 12 to the time t 13 (period P 13 ), is slightly closer to the center of the bed BD than the period P 12. It has been observed that during the period from time t 13 to time t 14 (period P 14 ), he was lying on the center of the bed BD.
  • the signals s 1 and s 4 of FIG. 4 indicate smaller load values than the period P 12
  • the signals s 2 and s 3 from the load detectors 12 and 13 arranged in the regions II and III are larger than the period P 12.
  • the load value is shown.
  • the center-of-gravity position calculation unit 31 determines the position G (X, Y) of the center of gravity G of the subject S on the bed BD based on the load signals s 1 to s 4 from the load detectors 11 to 14. Calculation is performed at a predetermined period T (for example, equal to the above sampling period of 5 milliseconds), and a temporal variation (center of gravity locus GT) of the position of the center of gravity G of the subject S is obtained.
  • T for example, equal to the above sampling period of 5 milliseconds
  • GT center of gravity locus GT
  • (X, Y) indicates coordinates on the XY coordinate plane, where X is taken in the longitudinal direction and Y is taken in the lateral direction with the center of the bed BD as the origin (FIG. 6).
  • G (X, Y) represents the coordinates of the load detectors 11, 12, 13, 14 as (X 11 , Y 11 ), (X 12 , Y 12 ), (X 13 , Y 13 ), (X 14 ), respectively. , Y 14 ), and the detected load values of the load detectors 11 , 12 , 13 , and 14 are respectively calculated as W 11 , W 12 , W 13 , and W 14 according to the following equations.
  • the center-of-gravity position calculation unit 31 calculates the time G of the position G (X, Y) of the center of gravity G while calculating the position G (X, Y) of the center of gravity G at a predetermined sampling period T based on the above formulas 1 and 2.
  • Change, that is, the center-of-gravity locus GT is obtained and stored in, for example, the storage unit 4.
  • FIG. 6 shows the position G (X P11 , Y P11 ) of the center of gravity G of the subject S on the bed BD at any time t 110 , t 120 , t 130 within the periods P 11 , P 12 , P 13 of FIG.
  • G (X P12 , Y P12 ), G (X P13 , Y P13 ), and the one-dot chain line arrow connecting P 11 , P 12 , P 13 is G from the position G (X P11 , Y P11 ) to G
  • the center of gravity locus GT of the center of gravity G of the subject S moving to (X P13 , Y P13 ) is shown.
  • the inventor of the present invention finds that the center-of-gravity locus GT of the subject S calculated by the center-of-gravity position calculation unit 31 mainly includes a locus of center-of-gravity movement caused by the three types of biological activities of the subject S. It was.
  • the first is a locus of center of gravity movement caused by a relatively large body movement accompanying the movement of the trunk (trunk) of the subject S such as turning over.
  • a relatively large body movement is referred to as “large body movement”.
  • Specific body movements are, for example, turning over and getting up.
  • a large body movement can be defined as a movement of the center of gravity of a relatively long distance that is greater than or equal to a predetermined distance that occurs within a predetermined period.
  • the center of gravity is larger than about a predetermined multiple compared to the movement distance of the center of gravity by small body movement.
  • the body movement to be moved can also be defined as a large body movement. Further, it may be defined by comparison with the amplitude of respiratory vibration described later.
  • the second is a locus of center of gravity movement caused by a relatively small body movement that does not involve movement of the torso (trunk) of subject S, such as movement of limbs and face.
  • a relatively small body movement is called “small body movement”.
  • the small body movement is, for example, movement of only the limbs and the head.
  • “large body movement” and “small body movement” are collectively referred to as “body movement”.
  • small body movement is defined from the viewpoint of the temporal variation of the position of the center of gravity, it can be generally defined that the small body movement is a movement of the center of gravity at a relatively short distance within a predetermined time. Further, it may be defined by comparison with the amplitude of respiratory vibration described later. Also, a body motion that causes a center of gravity movement that is a movement of the center of gravity for a relatively short distance within a predetermined time and that is not vibration in a certain direction may be defined as a small body motion. According to this definition, when focusing on the movement of the center of gravity, small body movements and breathing can be more clearly distinguished.
  • the third is the locus of gravity center movement caused by the subject's breathing.
  • Human breathing is performed by moving the thorax and diaphragm to expand and contract the lungs.
  • inhaling that is, when the lungs expand
  • the diaphragm descends downward
  • the internal organs also move downward.
  • exhaling that is, when the lungs contract
  • the diaphragm rises upward and the internal organs also move upward.
  • the inventor of the present invention has found through research that the center of gravity G vibrates substantially along the extending direction (body axis direction) of the spine as the internal organs move.
  • breathing vibration reciprocation along the body axis direction of the subject's center of gravity caused by the subject's breathing
  • breathing vibration trajectory the trajectory of breathing vibration
  • a waveform showing respiratory vibration in the time domain for example, a waveform showing the body axis direction as the vertical axis and time as the horizontal axis is called a “respiration waveform” of the subject.
  • stable body period a period in which the subject does not perform a large body movement
  • stable body period a period in which the subject does not perform a large body movement
  • stable body period a period in which the subject does not perform a large body movement
  • the body motion detection unit 32 detects whether or not body motion (large body motion, small body motion) is occurring in the subject S on the bed.
  • body motion large body motion, small body motion
  • the body movement determination step S1 is repeated again.
  • body movement has not occurred (S1: No)
  • the process proceeds to the subject number determination step S2.
  • the control unit 3 determines the number of subjects S on the bed BD.
  • the control unit 3 causes the vibration coordinate setting unit 34 to set vibration coordinates (details will be described later) of the subject S in the vibration coordinate setting unit 34 in the vibration coordinate setting step S3.
  • the control unit 3 causes the waveform separation unit 33 to perform the waveform separation step S6.
  • the waveform separation step S6 the vibration in which the respiratory vibrations of the plurality of subjects S are superimposed is separated, and the respiratory vibrations of each of the plurality of subjects S are taken out.
  • the control unit 3 causes the vibration coordinate setting unit 34 to perform the vibration coordinate setting step S3 for each of the respiratory vibrations separated and taken out, and sets the vibration coordinates of the respiratory vibrations of the plurality of subjects S.
  • the waveform drawing unit 35 respirates the subject S based on the vibration coordinates set in the vibration coordinate setting step S3 (if there are a plurality of subjects S, each breathing waveform of the subject S). Is drawn and displayed on the display unit 5.
  • the control unit 3 causes the drawing compensation unit 36 to execute the drawing compensation step S5 as necessary so that the display of the respiratory waveform on the display unit 5 is reliably continued during the execution of the waveform drawing step S4.
  • the drawing compensation unit 36 first determines whether or not the drawing state can be compensated. Compensate for the condition. On the other hand, if the drawing state cannot be compensated, the control unit 3 is informed accordingly. In this case, the control unit 3 stops drawing the respiration waveform and returns the process to the body movement determination process S1.
  • the number of the subject S existing on the bed BD is one, and the subject S is shown in FIGS.
  • An example will be described in which the breathing waveform of the subject S is drawn during the period in which the center of gravity movement indicating the locus is performed in 9 (c).
  • the center of gravity locus GT shown in FIG. 8 indicates the locus of center of gravity movement of the subject S for about 2 minutes calculated by the center of gravity position calculating unit 31.
  • the arrow indicates the direction in which the center of gravity G has moved.
  • the trajectory of movement of the center of gravity G from the area A to the area B and the trajectory of movement of the center of gravity G from the area B to the area C are trajectories of movement of the center of gravity due to large body movement accompanying the movement of the body of the subject S.
  • the center of gravity locus GT vibrates in the vertical direction (x direction) in the remaining section (period) in which the locus of gravity center movement due to these large body movements and the locus of gravity center movement due to small body movements are not recorded.
  • this section (period) it was observed that the subject S was sleeping at a fixed position without performing large body movements and small body movements. Therefore, the reciprocating motion (vibration) of the center of gravity G during these periods is a respiratory vibration along the body axis direction of the subject S, and the trajectory is a respiratory vibration trajectory.
  • the period in which the center of gravity locus GT in the section of point a to point b, point d to point s, and point t to point w is recorded Is the stable posture period, of which the center of gravity locus GT (ie, the respiratory vibration locus) of the sections from point a to point b, point d to point l, point m to point s, point t to point u, point v to point w ) Is the stable breathing period.
  • the center of gravity locus GT ie, the respiratory vibration locus
  • the body motion detection unit 32 detects whether body motion (large body motion, small body motion) is occurring in the subject S on the bed. Specifically, for example, the following method is used.
  • the movement of the body that occurs when the subject S performs a large body movement or a small body movement is accompanied by a much larger variation in the position of the center of gravity than the movement of the internal organs caused by the breathing of the subject S.
  • the movement speed (movement amount per unit time) of the center of gravity G caused by the large body movement or the small body movement is much higher than the movement speed of the center of gravity position movement caused by the breathing of the subject S.
  • the moving speed of the movement of the center of gravity G caused by the large body movement is larger than the moving speed of the movement of the center of gravity G caused by the small body movement.
  • the body motion detection unit 32 calculates the moving speed of the center of gravity G based on the change in the position of the center of gravity G of the subject S at each time stored in the storage unit 4, and the calculated speed exceeds a predetermined threshold. In this case, it is determined that the subject S is performing body movement, and if the calculated speed is equal to or less than a predetermined threshold, it is determined that the subject S is not performing body movement.
  • the body motion detection unit 32 determines that there is a body motion, and the control unit 3 returns the process to the body motion detection step S1.
  • the body motion detection unit 32 determines that there is no body motion in the body motion detection step S1, and the control unit 3 advances the process to the subject number determination step S2.
  • the presence or absence of body movement may be determined by other methods based on the definition of large body movement or small body movement.
  • the control unit (subject number determination unit) 3 determines whether or not the subject S on the bed BD is one person. Specifically, for example, the following method is used.
  • the position of the center of gravity G of the subject S vibrates on the bed BD according to the breathing of the subject S, and is from the load detectors 11 to 14 respectively disposed under the four legs of the bed BD.
  • Each of the load signals s 1 to s 4 also fluctuates at a period corresponding to the breathing of the subject S on the bed. Therefore, if Fourier transform is performed on at least one of the load signals s 1 to s 4 to obtain a frequency spectrum of a frequency band corresponding to respiration (about 0.2 Hz to about 0.33 Hz, hereinafter referred to as a respiration band).
  • the peak frequency appears at a position corresponding to the breathing frequency of the subject S.
  • the respiratory cycle varies depending on the sex, physique, vital capacity, etc. of the subject S. Therefore, when there are a plurality of subjects S on the bed BD, as many different peak frequencies as the number of subjects S appear in the frequency spectrum of the breathing band.
  • the control unit 3 causes the waveform separation unit 33 to perform Fourier analysis on at least one of the load signals s 1 to s 4 sent from the load detection unit 1 to calculate the frequency spectrum of the respiratory band, and the peak frequency that appears is calculated. If there is one, it is determined that there is one subject S, and if there are a plurality of peak frequencies that appear, it is determined that there are a plurality of subjects S.
  • the control unit 3 determines that the subject S is one (S2). : Yes).
  • the vibration coordinate setting unit 34 sets the vibration coordinates of the respiration vibration included in the center of gravity locus GT of the subject S, and calculates the displacement necessary for drawing the respiration waveform based on the set vibration coordinates.
  • the waveform drawing unit 35 draws the breathing waveform of the subject S based on the displacement calculated by the vibration coordinate setting unit 34.
  • the setting of the vibration coordinates means the “vibration origin” indicating the vibration center of the respiratory vibration and the direction of the vibration axis indicating the vibration direction of the respiratory vibration (the direction in which the body axis of the subject S extends). Means to set.
  • the vibration coordinate setting step S3 mainly includes a first temporary vibration coordinate setting step S301, a second temporary vibration coordinate setting step S302, a temporary vibration origin comparison step S303, and a vibration coordinate determination step S304.
  • the waveform drawing step S4 is performed partially in parallel with the vibration coordinate setting step S3.
  • the waveform drawing unit 35 uses the distance information output from the vibration coordinate setting unit 34 in the first temporary vibration coordinate setting step S301 and the second temporary vibration coordinate setting step S302 to perform temporary breathing of the subject S.
  • a waveform is drawn and displayed on the display unit 5.
  • the waveform drawing unit 35 draws the normal respiratory waveform of the subject S using the displacement information output from the vibration coordinate setting unit 34 based on the vibration coordinates determined in the vibration coordinate determination step S304. And displayed on the display unit 5.
  • the “temporary respiratory waveform” means the temporary vibration coordinates, that is, the temporary vibration origin and the temporary vibration axis before the vibration coordinates, that is, the vibration origin O and the vibration axis A are determined in the vibration coordinate determination step S304.
  • the “normal respiratory waveform” is a respiratory waveform drawn on the basis of the vibration origin O and the vibration axis A after the vibration coordinates are determined in the vibration coordinate determination step S304. means.
  • First provisional vibration coordinate setting step S301 As shown in FIG. 11A, the vibration coordinate setting unit 34 sets a point determined to have no body movement in the body movement determination step S1 as a first temporary vibration origin TO1 (an example of an initial origin). This point corresponds to the point d in the center of gravity locus GT illustrated in FIG. At this time, the waveform drawing unit 35 has not started drawing a respiratory waveform (FIG. 11B).
  • the vibration coordinate setting unit 34 sets a linear distance D 0 between the first temporary vibration origin TO1 and the center of gravity G moving from the first temporary vibration origin TO1 (FIGS. 12A and 13). (A)) is sequentially calculated, and the calculated value is output to the waveform drawing unit 35.
  • the waveform drawing unit 35 plots the value of the received linear distance D 0 in a graph in which the horizontal axis is the time axis (t axis) and the vertical axis is the distance axis (D 0 axis).
  • a respiration waveform is drawn (FIGS. 12B and 13B) and displayed on the display unit 5.
  • the vibration coordinate setting unit 34 observes the value of the distance D 0 between the first temporary vibration origin TO1 and the center of gravity G, obtains a point where the distance D 0 is maximum, and determines this point as the first extreme point EP1. (FIG. 13A). In the first extreme point EP1, change in the distance D 0 is turned from increasing to decreasing. The first extreme value point EP1 corresponds to the point e in the center-of-gravity locus GT illustrated in FIG.
  • the vibration coordinate setting unit 34 calculates an axis connecting the first temporary vibration origin TO1 and the first extreme value point EP1, and sets this as the first temporary vibration axis TA1,
  • One temporary vibration origin TO1 is set as the origin of the first temporary vibration axis TA1. That is, the vibration direction of the respiratory vibration started from the first temporary vibration origin TO1, that is, the direction of the vibration axis (the direction of the body axis) is provisionally determined to be the direction of the first temporary vibration axis TA1, and the vibration origin of the respiratory vibration is determined. Is temporarily determined to be the first temporary vibration origin TO1.
  • first extreme value point EP1 side of the first temporary vibration origin TO1 is set as the positive side of the first temporary vibration axis TA1, and the other side is set as the negative side of the first temporary vibration axis TA1.
  • the vibration coordinate setting unit 34 includes a perpendicular foot FP1 and a first provisional vibration origin TO1 extending from the center of gravity G moving from the first extreme value point EP1 to the first provisional vibration axis TA1. successively calculating a distance D 1 of the between, and sends the calculated value to the waveform drawing unit 35.
  • the waveform drawing unit 35 draws a temporary respiratory waveform of the subject S based on the received calculated value (FIG. 15B, FIG. 16B) and displays it on the display unit 5.
  • the vibration coordinate setting unit 34 a distance D 1 (FIG. 15 (a), the FIG. 15 (b), the FIG. 16 (a), the to FIG. 16 (b)) was observed, and the maximum that distance D 1 is the negative side This point is obtained, and this point is set as the second extreme point EP2.
  • change in the distance D 1 is turned from increasing to decreasing.
  • the first extreme value point EP2 corresponds to the point f in the center-of-gravity locus GT illustrated in FIG.
  • the center of gravity G and the first temporary vibration point are identified.
  • the second extreme point may be specified using a linear distance from the vibration origin TO1.
  • the vibration coordinate setting unit 34 calculates an axis connecting the first extreme value point EP1 and the second extreme value point EP2, and uses this as the second temporary vibration axis (temporary vibration).
  • Axis TA2 and an intermediate point between the first extreme value point EP1 and the second extreme value point EP2 is a second temporary vibration origin (temporary vibration origin) TO2. That is, the direction of the vibration axis of the respiratory vibration (the direction of the body axis) started from the first temporary vibration origin TO1 is tentatively determined to be the direction of the second temporary vibration axis TA2, and the vibration origin of the respiratory vibration is determined as the second temporary vibration origin. Temporarily re-determine that the vibration origin is TO2.
  • one side of the second temporary vibration origin TO2 is set as the positive side of the second temporary vibration axis TA2, and the other side of the second temporary vibration origin TO2 is set.
  • the side is set as the negative side of the second temporary vibration axis TA2.
  • the vibration coordinate setting unit 34 is between the first temporary vibration origin TO1 set in the first temporary vibration coordinate setting step S301 and the second temporary vibration origin TO2 set in the second temporary vibration coordinate setting step S302. Is determined, and it is determined whether or not the calculated distance is equal to or less than a predetermined value.
  • the predetermined value may be 10% of the distance between the first extreme value point EP1 and the second extreme value point EP2.
  • the vibration coordinate setting unit 34 is illustrated in FIG.
  • the second temporary vibration origin TO2 is determined as the vibration origin O of respiratory vibration
  • the second temporary vibration axis TA2 is determined as the vibration axis A of respiratory vibration
  • the vibration coordinates are determined. That is, it is determined that the center of gravity G of the subject S with the body axis direction in the direction of the vibration axis A is oscillating along the vibration axis A with the vibration origin O as the vibration center by the breathing of the subject S.
  • the vibration coordinate setting unit 34 determines whether the distance between the first temporary vibration origin TO1 and the second temporary vibration origin TO2 exceeds a predetermined distance as a result of the comparison (S303: No). If the distance between the first temporary vibration origin TO1 and the second temporary vibration origin TO2 exceeds a predetermined distance as a result of the comparison (S303: No), the vibration coordinate setting unit 34 The vibration coordinate setting step S305 and the temporary vibration origin comparison step S306 are executed.
  • the vibration coordinate setting unit 34 calculates an axis connecting the second extreme value point EP2 and the third extreme value point, and sets this as the third temporary vibration axis, and the second extreme value point EP2 and the third extreme value.
  • An intermediate point with the point is defined as a third temporary vibration origin TO3.
  • the vibration coordinate setting unit 34 sets the second temporary vibration origin TO2 set in the second temporary vibration coordinate setting step S302 and the third temporary vibration coordinate setting.
  • a distance from the third temporary vibration origin TO3 set in step S305 is calculated, and it is determined whether or not the calculated distance is equal to or less than a predetermined value.
  • the third temporary vibration origin TO3 is set as the respiratory vibration oscillation origin O.
  • the third provisional vibration axis TA3 is determined as the vibration axis A for respiratory vibration (vibration coordinate determination step S304).
  • the vibration coordinate setting unit 34 After determining the vibration origin O and the vibration axis A in the vibration coordinate determination step S304, the vibration coordinate setting unit 34, as shown in FIG.
  • the distance D to O is sequentially calculated, and the calculated value is sent to the waveform drawing unit 35 as the displacement of the respiratory waveform.
  • the waveform drawing unit 35 draws a normal respiration waveform based on the received displacement value (FIG. 19B) and displays it on the display unit 5.
  • the position of the vibration origin is different between the determined vibration coordinate and the temporary vibration coordinate set immediately before. Therefore, when drawing of the respiration waveform based on the determined vibration coordinates is started, as shown in FIG. 19B, the newly drawn normal respiration waveform and the temporary respiration that has been drawn so far are displayed. There may be a slight deviation from the waveform. Based on the difference between the temporary vibration coordinates and the determined vibration coordinates, the drawn temporary breathing waveform may be corrected and redrawn to eliminate this deviation.
  • the drawing compensation unit 36 corrects the drawing position by the following method.
  • the drawing compensation unit 36 includes a predicted waveform generation unit 361 and a correction distance calculation unit 362. Then, in the drawing compensation step S5, the drawing compensation unit 36 executes a predicted waveform generation step S501 and a correction distance calculation step S502 as shown in FIG.
  • the predicted waveform generation step S501 and the correction distance calculation step S502 executed by the drawing compensation unit 36 will be described.
  • Estimated waveform generation unit 361 of the drawing compensator 36 generates the estimated waveform generation step S501, for example, already the most recent one period of the respiratory waveform W 1 that is drawn on the display unit 5 as the estimated waveform W S, the estimated waveform W S is drawn on the display unit 5 so as to be continuous with the respiratory waveform W 1 (FIG. 23. However, the predicted waveform W S may not be drawn on the display unit 5).
  • the respiratory waveform W 1 drawn with solid lines, by drawing a predicted waveform W S in dashed lines, are distinguished respiration waveform W 1 and the estimated waveform W S.
  • the values of the first threshold value Th 1 and the second threshold value Th 2 may be appropriately set according to the size of the display area of the display unit 5.
  • the control unit 3 determines that no body movement has occurred, and executes the waveform drawing step S4. Then, in the waveform drawing step S4, the waveform drawing unit 35 continues drawing the respiratory waveform based on the actual measurement point D (t 0 ) without correcting the drawing position.
  • the control unit 3 determines that a small body movement has occurred, and performs the following compensation operation while performing the waveform drawing step S4. Execute.
  • the waveform drawing unit 35 draws the measured point D (t 0 ) by moving (offset) the distance d (t 0 ) in the direction of the vibration axis A. That is, the distance d (t 0 ) is used as the correction distance as it is.
  • the control unit 3 determines that a large body movement has occurred and executes the body movement determination step S1 again.
  • the drawing compensation step S5 even if a small body motion occurs during drawing of the respiratory waveform, the respiratory waveform before and after the small body motion is continuously drawn within the display range of the display unit 5. can do.
  • the vibration coordinates can be set again, and the waveform drawing can be performed through the above process.
  • the step of drawing the respiratory waveforms of a plurality of (two) subjects S on the bed BD focuses on the difference from the step of drawing the respiratory waveform of the single subject S described above.
  • the body movement determination step S1 determines the presence or absence of body movement of the subject S based on the moving speed of the center of gravity G on the bed BD, as in the case where the subject S is alone.
  • the control unit 3 determines that the body movement of the subject S has been lost when all of the body movements of the plurality of subjects S have stopped.
  • the waveform separation unit 33 performs a Fourier transform on at least one of the load signals s 1 to s 4 to obtain a breathing band (about 0.2 Hz to about 0.33 Hz). Obtain the frequency spectrum.
  • the control unit 3 determines that there are a plurality of subjects S (S2: No).
  • the waveform separation unit 33 obtains a load component of each load signal for each identified frequency when a plurality of peak frequencies are identified in the subject number determination step S2.
  • These load components can be obtained, for example, by bandpass filter processing for each of the load signals s 1 to s 4 .
  • four load components s 11 , s 21 , s 31 , and s 41 corresponding to the peak frequency ⁇ 1 and the peak frequency ⁇ are obtained.
  • the waveform separation unit 33 outputs four load components corresponding to the peak frequencies ⁇ 1 and ⁇ 2 to the gravity center position calculation unit 31.
  • the center-of-gravity position calculation unit 31 calculates the center-of-gravity position and the center-of-gravity locus corresponding to each of the peak frequencies ⁇ 1 and ⁇ 2 (that is, each of the subjects S). Calculation is performed in the same manner as in the gravity center locus calculation step S02.
  • the vibration coordinate setting step S3 After the center of gravity locus for each of the plurality of subjects S is obtained in the waveform separation step S6, the vibration coordinate setting step S3, the waveform drawing step S4, and the drawing compensation step S5 based on the center of gravity locus of each of the plurality of subjects S. Is executed. The details are as described above by taking the case where the subject S is alone as an example.
  • the respiratory waveform of the subject can be presented in almost real time.
  • the vibration coordinate setting unit 34 sets a temporary vibration origin immediately after the subject S enters the stable breathing period, and then the distance D 0 of the center of gravity position therefrom. start the calculation, before setting the vibration coordinates, waveform drawing unit 35, to start drawing of the respiratory waveform on the temporary coordinate system based on the calculated value of the distance D 0. Therefore, the respiratory waveform can be displayed on the display unit 5 almost immediately after the large body movement or the small body movement is finished.
  • the drawing compensation step S5 generates the estimated waveform W S based on past respiratory waveform, the measured points D at the current sampling time t 0 (t 0) and the predicted point W
  • the drawing position of the actual measurement point D (t 0 ) is corrected according to the distance d (t 0 ) between S (t 0 ). Therefore, even if the actual measurement point D (t 0) is deviated from the prediction point W S (t 0), immediately to correct the drawing position of the measured point G (t 0), the display unit 5 to continue the respiratory waveform Can be displayed.
  • the number of subjects S on the bed BD is determined in the subject number determination step S2.
  • the respiratory vibrations of the subjects S can be separated in the waveform separation step S6, and the respiratory waveforms of the subjects S can be drawn. For this reason, for example, even if the patient's family is lying on the bed BD on which one patient lies, the patient's respiratory waveform can be reliably monitored.
  • the biological information monitoring system 100 calculates the respiratory rate of the subject S using the load detectors 11 to 14 disposed under the legs of the bed BD. Therefore, it is not necessary to attach a measuring device to the body of the subject S, and the subject S does not feel uncomfortable or uncomfortable. ⁇ Modification>
  • the vibration coordinate setting step S3 is started regardless of whether or not the subject S is alone.
  • the number-of-subjects determination step S2 and the waveform separation step S6 are executed in parallel with the vibration coordinate setting step 3, and if there are a plurality of subjects S, a plurality of peak frequencies specified in the number-of-subjects determination step S2 (that is, a plurality of subjects) Based on the subject S), the center of gravity locus of each of the plurality of subjects S is separated in the waveform separation step S6, and based on this, the vibration coordinate setting step S3, the waveform drawing step S4, and the drawing compensation step S5 are executed.
  • the vibration coordinate setting unit 34 of the biological information monitoring system 100 calculates the distance between the temporary vibration origin set last and the temporary vibration origin set immediately before it in the temporary vibration origin comparison steps S303, S306, and the like. Although it has been determined whether or not the vibration origin A can be set by comparing with a predetermined value, the present invention is not limited to this.
  • the vibration coordinate setting unit 34 sets the provisional vibration origin and the provisional vibration axis a predetermined number of times, and determines the last provisional vibration origin and provisional vibration axis as the vibration origin O and the vibration axis A. Also good.
  • the vibration coordinate setting unit 34 may set the temporary vibration origin and the temporary vibration axis for a predetermined number of times, and determine the average of them as the vibration origin O and the vibration axis A.
  • the waveform drawing unit 35 of the biological information monitoring system 100 of the above embodiment receives information on the coordinates of the Nth extreme value point EPN, the inclination of the Nth temporary coordinate axis TAN, and the like from the vibration coordinate setting unit 34, and based on these information You may adjust the scale of a graph area suitably. For example, a distance in the second temporary vibration axis TA2 direction between the first extreme value point EP1 and the second extreme value point EP2 or a distance D (displacement) calculated using the determined vibration origin O and vibration axis A.
  • the scale of the vertical axis (distance DN axis, displacement axis) of the graph area can be adjusted based on the maximum value (amplitude). Thereby, the respiration waveform of the optimal scale suitable for observation can always be displayed on the display part 5.
  • the drawing compensation step S5 is performed on the respiration waveform drawn through the vibration coordinate setting step S3 and the waveform drawing step S4.
  • the present invention is not limited to this, and the respiration waveform drawn by other methods is used.
  • the drawing compensation step S5 may be applied.
  • the drawing compensation unit 36 detects the occurrence of a small body motion or a large body motion based on the distance between the predicted point W S (t 0 ) and the actual measurement point D (t 0 ). Is not limited. For example, when the vibration coordinate setting unit 34 determines that the distance between the determined position of the vibration origin O and the position of the center of gravity G of the subject S exceeds a predetermined value, a small body movement or a large body movement occurs. It may be determined that the stable breathing period has ended, and the controller 3 may return the process to the body movement determination step S1 when a large body movement occurs.
  • the predetermined value can be set based on the distance between the first extreme value point EP1 and the second extreme value point EP2, for example.
  • the estimated waveform generation step S501 but the most recent one period of the respiratory waveform W 1 is drawn as a predicted waveform W S, not limited to this, the model of the past two cycles or more respiratory waveform
  • the modeled waveform may be used as the predicted waveform W S.
  • the estimated waveform W S may if already distinguished from the respiratory waveform W 1 that is drawn on the display unit 5, for example, may be drawn respiratory waveform W 1 and the estimated waveform W S in different colors.
  • the control unit 3 causes a small body movement.
  • the average value of the distances d (t n ) may be used as the correction distance. That is, the actual measurement points D (t n ) may be drawn by moving in the direction of the vibration axis A by the average value of the distance d (t n ). According to this method, it is possible to improve the accuracy of determination of small body movements.
  • the predetermined time for example, 1/4 period predicted waveform W S
  • the distance d (t n ) is calculated and the distance d (t n ) is a constant value and is not less than the first threshold Th 1 and not more than the second threshold Th 2
  • the control unit 3 has a small body movement. It may be determined that the distance has occurred, and the distance d (t n ) may be used as the correction distance.
  • the measured points D (t n ) may be drawn by moving the measured points D (t n ) in the direction of the vibration axis A by the distance d (t n ). According to this method, the accuracy of determination of small body movement can be further increased.
  • the correction distance calculation unit 362 sets ⁇ x such that the integral value expressed by the following (Equation 3) is minimized.
  • a value may be calculated, and the ⁇ x may be used as a further correction distance.
  • T means the period of the predicted waveform W S
  • W S (t) is an equation indicating the fluctuation of the prediction point as a function of time t
  • D (t) is the fluctuation of the actual measurement point as a function of time t. It is a formula.
  • ⁇ x means a further correction distance.
  • each respiration waveform is calculated from the load component corresponding to one specific frequency. Therefore, it becomes a substantially sine wave.
  • an actual respiration waveform is obtained by superimposing a plurality of frequency components such as a frequency component resulting from a difference in inspiratory and expiratory speeds and a difference in hold period in each. Therefore, when the breathing pattern of each subject S is modeled in advance, a plurality of peak frequencies are selected from the frequency profile as shown in FIG. 26, and the load component corresponding to the selected peak is actually obtained. A respiration waveform closer to the respiration waveform may be drawn.
  • the respiratory waveform of each subject S may be made to follow the changing frequency of the subject S by specifying a frequency at regular time intervals and calculating a load component corresponding to the specified frequency.
  • the Fourier integration time is dynamically changed from a time that is back by a predetermined time length ⁇ t from the present to the present.
  • the coefficient peak that is seen from the time that is a predetermined time length ⁇ t to the present is calculated.
  • the change from the already specified frequency to the current frequency can be captured in time series.
  • the respiration waveform of each subject S can be made to follow the change of the frequency of the subject S.
  • the number of subjects S on the bed and the respiration waveform of each subject S are obtained by determining the number of peak frequencies in the respiration band.
  • various biological information of each subject S can be separated. For example, by identifying a frequency peak in the range of about 0.5 to about 3.3 Hz in the subject number determination step S2, in the waveform separation step S6, waveforms representing the heartbeats of a plurality of subjects S are separated and monitored. You can also.
  • the waveform separation step S6 has been described on the assumption that the plurality of subjects S are all humans.
  • the present invention is not limited to this.
  • one subject S and a device that generates periodic vibrations on a bed Even if there is such a case, the respiratory vibration of one subject S can be separated from the periodic vibration by the apparatus.
  • Control part 3 of living body information monitoring system 100 of the above-mentioned embodiment can also ask for subject's S respiration rate by the following methods. Specifically, for example, after the vibration origin O and the vibration axis A are determined, the vibration coordinate setting unit 34 continues to specify the extreme points, and the control unit 3 determines the extreme points identified per unit time. The respiration rate of the subject S can be obtained based on the number of.
  • the biological information monitoring system 100 according to the above embodiment may not include at least one of the vibration coordinate setting unit 34, the drawing compensation unit 36, and the subject number determination unit in the control unit 3.
  • the load detectors 11, 12, 13, and 14 are not limited to load sensors using beam-type load cells, and for example, force sensors can also be used.
  • the number of load detectors is not limited to four. Five or more load detectors may be used with additional legs on the bed BD. Or you may arrange
  • the load detector 11, 12, 13 and 14 are arranged under the bed casters C 1 attached to the lower end of the leg of the BD, C 2, C 3, C 4
  • Each of the load detectors 11, 12, 13, and 14 may be provided between the four legs of the bed BD and the floor plate of the bed BD, or the four legs of the bed BD can be divided vertically. For example, it may be provided between the upper leg and the lower leg.
  • the load detectors 11, 12, 13, and 14 may be integrated with the bed BD, and a bed system BDS including the bed BD and the biological information monitoring system 100 of the present embodiment may be configured (FIG. 27).
  • the load detector provided on the bed means a load detector provided between the four legs of the bed BD and the floor plate of the bed BD as described above, an upper leg, It means a load detector provided between the lower leg.
  • a signal amplification unit that amplifies the load signal from the load detection unit 1 and a filtering unit that removes noise from the load signal are provided between the load detection unit 1 and the A / D conversion unit 2. May be.
  • the display unit 5 is not limited to displaying information on the monitor so that the user can visually recognize it.
  • the display unit 5 may be a printer that periodically prints and outputs the breathing state (respiration rate, respiratory ventilation), heartbeat state, and physical condition of the subject S, or if the sleep state is on, the blue lamp is lit, the awakening state In this case, a simple visual expression such as lighting of a yellow lamp and lighting of a red lamp in an apnea state may be used.
  • the display unit 5 may convey the breathing state and physical state of the subject S to the user by voice.
  • the biological information monitoring system 100 may not have the display unit 5 and may only have an output terminal for outputting information.
  • a monitor (display device) or the like for performing display is connected to the biological information monitoring system 100 via the output terminal.
  • reporting part 6 of the said embodiment performed alerting
  • reporting part 6 may be the structure which alert
  • the biological information monitoring system 100 according to the above embodiment may not have the notification unit 6.
  • the present invention is not limited to the above embodiments, and other forms conceivable within the scope of the technical idea of the present invention are also included in the scope of the present invention. .
  • the breathing vibration of the subject can be presented to the user in a good state with little interruption or time lag
  • data suitable for observation is mainly provided by the user who is a doctor.

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PCT/JP2017/018338 2016-05-17 2017-05-16 呼吸波形描画システム及び生体情報モニタリングシステム Ceased WO2017199945A1 (ja)

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EP17799369.8A EP3459452B1 (en) 2016-05-17 2017-05-16 Respiration waveform drawing system and biological information monitoring system
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CN109475324A (zh) 2019-03-15
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