WO2013170035A1 - Système et procédé de surveillance vidéo de mouvement, de respiration et de rythme cardiaque sans fixation - Google Patents

Système et procédé de surveillance vidéo de mouvement, de respiration et de rythme cardiaque sans fixation Download PDF

Info

Publication number
WO2013170035A1
WO2013170035A1 PCT/US2013/040357 US2013040357W WO2013170035A1 WO 2013170035 A1 WO2013170035 A1 WO 2013170035A1 US 2013040357 W US2013040357 W US 2013040357W WO 2013170035 A1 WO2013170035 A1 WO 2013170035A1
Authority
WO
WIPO (PCT)
Prior art keywords
signal
domain
subject
respiration
time
Prior art date
Application number
PCT/US2013/040357
Other languages
English (en)
Inventor
Edward RIVAS
Eric NELEIGH
Arturo Alejo AYON
Original Assignee
Technophysics Solutions, Corporation
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Technophysics Solutions, Corporation filed Critical Technophysics Solutions, Corporation
Publication of WO2013170035A1 publication Critical patent/WO2013170035A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—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
    • A61B5/683—Means for maintaining contact with the body
    • A61B5/6832—Means for maintaining contact with the body using adhesives
    • A61B5/6833—Adhesive patches
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2503/00—Evaluating a particular growth phase or type of persons or animals
    • A61B2503/04—Babies, e.g. for SIDS detection
    • 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
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A61B5/0816—Measuring devices for examining respiratory frequency

Definitions

  • the present invention relates to a system and method directed to attachment free respiration, heartbeat, motion, and video monitoring of a subject. More specifically, the present invention relates to a system and method for attachment free respiration, heartbeat, motion, and video monitoring of a subject through a sensor pad communicatively coupled to a base station and the base station communicatively coupled to a remote monitoring device.
  • the first option which is passive, is to adhere to the recommendations from the major pediatric physician's group on safe sleeping including having the infant sleep on their back, removing all possible suffocation hazards from the sleeping space, and to have the infant sleep without blankets. This approach may indeed reduce the likelihood of S.I.D.S. but as a mere preventative measure, it still leaves the parent wondering about the status of their infant at any given time.
  • a second option is to employ active monitoring of the infant.
  • a first example of a monitoring system in the prior art is described in U.S. Pat. No. 7,666,151 issued on Feb. 23, 2010 to Patrick K. Sullivan et al.
  • the monitoring system also utilizes a different process to extract the components of the signal related to motion, respiration, and breathing.
  • the present invention proposes a novel system and method for attachment free monitoring of a subject's motion, respiration, and heartbeat.
  • the present invention therefore, provides a system and method directed to attachment free monitoring of a subject.
  • the attachment free monitoring system obtains a subject's respiration, heartbeat, and motion through filtering of signals obtained from piezo benders mounted to a monitoring pad containing isolation dampeners and a layer of material for force distribution.
  • the monitoring pad provides the signal that is then filtered to isolate various components representing the subject's motion, respiration, and heartbeat.
  • the monitoring system is comprised of a monitoring pad, a base station, and a monitoring display device such as a smart phone or web interface.
  • the components of the system are communicatively coupled through wireless means.
  • the monitoring system additionally contains a visual monitoring device. The system may be programmed to provide alerts and subject stimulation based on various trigger points tied to thresholds in the measurements.
  • the present invention discloses a system and method directed to attachment free monitoring of a subject's respiration, heartbeat, and motion. More specifically, the present invention relates to a system and method for monitoring of a subject's respiration, heartbeat, and motion through a sensor pad communicatively coupled to a base station and the base station communicatively coupled to a remote monitoring device.
  • FIG. 1 is a component diagram of the monitoring system in accordance with embodiments of the disclosure.
  • FIG. 2 is an illustration of the piezo benders mounting configuration on isolation dampening material in accordance with embodiments of the disclosure
  • FIG. 3 is a side view of the monitoring pad comprising a rigid base, sensor grid, and a layer of foam in accordance with embodiments of the disclosure;
  • FIG. 4 is a schematic layout of the monitoring pad illustrating the various components in accordance with embodiments of the disclosure
  • FIG. 5 is a schematic layout of the base station illustrating the various components in accordance with embodiments of the disclosure.
  • FIG. 6 is a block flow diagram for the process utilized in the base station in accordance with embodiments of the disclosure.
  • FIG. 7 is a block flow diagram for the Fast Fourier Transform process utilized in the base station for the heart beat rate calculations in accordance with embodiments of the disclosure
  • FIG. 8 is a block flow diagram for the auto-correlation process utilized in the base station for the heart beat rate calculations in accordance with embodiments of the disclosure
  • FIG. 9 is a block flow diagram for the Fast Fourier Transform process utilized in the base station for the respiration rate calculations in accordance with embodiments of the disclosure.
  • FIG. 10 is a block flow diagram for the auto -correlation process utilized in the base station for the respiration rate calculations in accordance with embodiments of the disclosure.
  • FIG. 11 is a signal frequency versus magnitude representation to determine the subject's active or inactive status in accordance with embodiments of the disclosure.
  • the invention is an attachment free motion, respiration, heartbeat and video monitoring system for humans and animals.
  • the system is comprised of a monitoring pad 110, base station 120, and monitoring devices such as a personal computer 130 or mobile device 140.
  • the monitoring pad 110 contains no external wires or straps that may pose a hazard to the subject being monitored. For example, external wires and straps could cause the subject being monitored to become entangled or could be objects the subject being monitored could choke on.
  • the subject lies upon the monitoring pad 110, which detects the motion of the subject through piezo benders integrated into the monitoring pad 110.
  • Examples of motions picked up by the monitoring pad 110 include but are not limited to physical movements (such as the movements of limbs and falling out of the bed), respiration, and heartbeat. These motions are captured and transmitted wirelessly to the base station 120.
  • the base station 120 contains the means for receiving and storing data as well as performing calculations on that data.
  • the base station 120 takes the data captured and isolates the respiration and heartbeat data and then transmits the results to the monitoring devices 130, 140. Transmission of this data may take place through wireless or non-wireless means.
  • the base station 120 is also able to send an alarm (visual, audible, physical) to the monitoring devices 130, 140 based on preset thresholds or if the energy of the signal drops to a preset level.
  • the monitoring devices 130, 149 may be web enabled and/ or contain software applications as a graphical user interface (GUI) for the presentation layer of the monitoring system.
  • Wireless communications may be established by having the base station 120 connected to a wireless router as one means for this type of communication.
  • GUI
  • Fig. 2a and 2b an illustration of the piezo benders 210 mounting configuration on isolation dampening material 220.
  • Fig. 2a illustrates a top view of the piezo bender 210.
  • Fig. 2b a side view of the mounting, the piezo benders 210 are mounted or coupled at the perimeter of the rings of isolation dampening material 220. That is, the isolation dampening material 220 is a ring with the center being open which allows the piezo benders 210 to be deflected more easily.
  • the dampening material is Sorbothane of durometer 40 and supports the perimeter of a round piezo bender 210.
  • Fig. 3 a side view of a monitoring pad comprising a rigid base 330, an array of piezo benders also termed a sensor grid 320, and a layer of material such as foam 310.
  • the monitoring pad 110 consists of an array of piezo benders 320 mounted to the rigid base 330 by way of isolation dampeners, a layer of material 310 over the array of piezo benders 320 for force distribution and the subject's comfort, electronics to convert the piezo bender signals to digital form, and means to transmit the digital signals to the base station 120.
  • the monitoring pad 110 would also contain the means to provide physical stimulation to the subject such as vibration and motions to awaken the subject.
  • the layer of foam 310 is the isolation dampening material Sorbothane.
  • the layer of foam 310 is placed over the sensor grid 320 to allow for better force distribution among the individual sensors in the sensor grid 320.
  • this layer of foam 310 would have a one -inch thickness with a firmness rating of 40.
  • the monitoring pad 110 can be configured or manufactured to take on various shapes and sizes to adequately cover the area to be monitored.
  • Fig. 4a and 4b a schematic layout of the monitoring pad illustrating the various components and layout for design purposes.
  • the electronics compartment 410, piezo benders 420, electronic box connector 430, and the wiring channels 440 can bee seen.
  • the rigid base 330 has dimensions of fifteen inches by twenty-seven inches to fit in a standard baby bassinette.
  • the sensor grid 320 has a layout of twelve piezo benders 420 in a four by three arrangement being five inches apart from center to center in the four piezo bender 420 direction and three point seven five inches apart in the three piezo bender 420 direction wired in series to an A/D input.
  • piezo benders 420 are wired in series from ground to a center biased 1.1 V source and six peizo benders 420 are wired in series from the same point to 2.2 V, which is the maximum input range of the A/D used.
  • a microprocessor controls the timing of the acquisition as well as the transmission of collected data to the base station 120.
  • An example of a processor used for data acquisition of the signal generated by the PUI piezo bender array is the Microchip PIC18F25K80. Force applied to any individual piezo bender 420 will be additive to the output of all other piezo benders 420 from the point of view of the A/D input.
  • the analog input can also be amplified through one of four amplifications (lx, 2x, 4x, 8x) before the A/D conversion process. This amplification is software selectable.
  • Data transmission to the base station 120 is accomplished by way of ANT Wireless Personal Network protocol. Power is supplied by two AA batteries which are contained with all the digital electronics in a compartment 410 isolated form the piezo array. While this is illustrative of one embodiment, other embodiments may employ alternative power sources such as capacitors, solar, wireless transmission, motion of the subject, or even thermal energy from the subject being monitored. A fifteen hertz sampling rate provides good resolution of biological indicators of interest while allowing for low power consumption for acquisition and transmission of data. In other embodiments the rigid base is soft and/or flexible as illustrated in Fig. 4b.
  • FIG. 4b is a perspective view of the monitoring pad illustrating the electronics compartment 410, the piezo benders 420, the soft base 430, and the foam layer 440.
  • An advantage of having a soft base is allowing the piezo benders to deflect freely without any rigid support.
  • the base station 120 contains the means such as electronic to receive data, process data to isolate the components for respiration and heartbeat, store data, transmit current or stored data to another device such as the monitoring devices 130, 140, determine of an alert should be triggered, and transmit the alert status to another device such as the monitoring devices 130, 140.
  • the base station 120 is comprised of a microprocessor (within the base station), local display 530, camera 520, microphone 590, wi-fi antenna 510, network connection 560, external power connection 580, control pad 550, indicator lights 540, 555, and mounting point 570.
  • An example of an implementation is a Freescale IMX53 microprocessor based system with the capability to stream video, audio, signal data, processed data, and calculated data to monitoring devices 130, 140 or any other devices utilized in the monitoring system.
  • the processor can be running Ubuntu linux.
  • the camera 520 which allows for video of the subject to be taken and broadcast to another device.
  • the camera 520 has an infrared illumination assist consisting of a ring of infrared LED which provide illumination of the subject with light detectable by the camera 520, but will not disturb the subject.
  • the local display 530 and control pad 550 allows for basic controls and status displays of the system locally.
  • the wi-fi antenna 510 and network connection 560 allows for communications of the base station 120 with other devices such as the remote devices 130, 140.
  • the indicator lights 540, 555 allow for easy visual status identification when the local display 530 is not viewable.
  • the mounting point 570 allows for the base station 120 to be mounted easily to items such as a wall bracket or stand. Data collected and calculations performed can be stored in long-term memory in the form of a searchable database.
  • An external device connected by way of a wireless router, can perform the searches.
  • the microphone 590 is utilized to obtain audio feedback of the monitoring environment.
  • the external power connection 580 is utilized to connect the base station to an external power source.
  • Fig. 6 a block flow diagram for the process utilized in the base station 120.
  • the DC component or average is subtracted from the time based signal collected from the monitoring pad 110.
  • This signal is passed through a 3 rd order Butterworth filter for extracting the signals of interest for both the respiration and heart beat information.
  • a band pass region of between 0.33Hz and 1.33Hz is utilized for detecting the respiration information such as breath rate.
  • a band pass region of between 1.33Hz and 3.00 Hz is utilized for detecting the heart beat information such as rate.
  • a filter region can be chosen for a specific gender, age range, or species.
  • FIG. 7 and Fig. 9 block diagrams for the Fast Fourier Transform (FFT) process utilized in the base station 120 for the heart beat rate and respiration rate calculations.
  • FFT Fast Fourier Transform
  • a Fast Fourier Transform is performed on a 256 sample set of the filtered respiration and heart beat signal respectively, which has been windowed by a 256 point Hanning filter.
  • the frequency of the highest energy content is considered to be the corresponding respiration rate or heart beat rate for the latest calculation iteration.
  • block diagrams for the auto correlation process utilized in the base station 120 for the heart beat rate and respiration rate calculations Another aspect of the algorithm is the auto correlation of a 64 point sample set is used to determine the fundamental period of respiration rate or heart beat rate, which would allow for quicker calculation times. To reduce the chances of a spurious reading to trigger a false alarm, an immediate change of calculated rates may not trigger an alarm. Instead, a moving average window is utilized to determine if an immediate reading is likely to be accurate.
  • Fig. 8 For the case of respiration rate, a running average of calculated respiration rates from the last three calculations is kept. If the current calculation falls within a window of the current average multiplied by 0.9 and the current average multiplied by 1.1, it is deemed to be accurate. If it falls outside this window, the previous calculated respiration rate is held for an additional iteration. However, the new calculated value is used for the purposes of keeping the running average. [0032] Reference is next made to Fig. 10. In the case of heart beat rate, a running average of calculated heart beat rates from the last three calculations is kept. If the current calculation falls within a window of the current average multiplied by 0.8 and the current average multiplied by 1.2, it is deemed to be accurate.
  • a set of alarms can be issued depending on the respiration rate calculated or the heart beat rate calculated, as well as the overall energy detected in the biological indicators of interest.
  • An overall energy level in the region of interest can indicate a problem with a shallowness of breathing or weak pulse or that the subject is moving or thrashing around. If the subject is moving around too much to get a clear respiration rate or heart beat rate, an active signal can be sent that there is motion on the monitoring pad 110, but no clear reading of biological indicators.
  • a signal frequency versus magnitude representation to determine the subject's active or inactive status.
  • the subject lies upon the monitoring pad 110, which detects the motion of the subject through piezo benders integrated into the monitoring pad 110.
  • Examples of motions picked up by the monitoring pad 110 include but are not limited to physical movements (such as the movements of limbs and falling out of the bed), respiration, and heartbeat.
  • the differentiating criteria for determining whether the subject is moving, having normal respiration and heartbeat or is missing is done using a combination of the magnitude of the sampled signal as well as the frequency of the energy peaks in the frequency domain representation, represented in Fig. 11.
  • the circuitry is configured to amplify the sensor signal so that the dynamic range is matched to the input range of the analog to digital converter.
  • the system cannot calculate the vital signs but it can be inferred that if the signal magnitude 1100 exceeds a certain threshold 1130 then we can safely assume that the subject is alive but active. In the infant monitor implementation, this state is called "Baby Active". If the signal magnitude falls below a certain minimum threshold 1140 then the subject is assumed to have very shallow breathing movements or is no longer on the sensor pad.
  • 1110 and 1120 indicate the algorithm's low and high frequency thresholds for a frequency peak, outside of which an alarm is triggered.
  • the system and method is directed to attachment free monitoring as described herein and provides for an effective and efficient means for monitoring a subject's motion, respiration, and heartbeat.
  • video monitoring is incorporated as part of the device and method.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Surgery (AREA)
  • Biophysics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Pathology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Measuring And Recording Apparatus For Diagnosis (AREA)

Abstract

La présente invention concerne un système et un procédé de surveillance sans fixation de la respiration, du rythme cardiaque et du mouvement d'un sujet. Dans un mode de réalisation, ledit système de surveillance est constitué d'un coussinet de surveillance, d'une station de base, et d'un dispositif d'affichage de surveillance tel qu'un téléphone intelligent ou une interface Web. Dans un autre mode de réalisation, les composants du système sont accouplés pour communiquer par des moyens sans fil. Dans un autre mode de réalisation, le système de surveillance comprend en outre un dispositif de surveillance visuelle. Le coussinet de surveillance fournit le signal qui est filtré pour isoler divers composants représentant le mouvement, la respiration et le rythme cardiaque du sujet. Le système peut être programmé pour fournir des alertes et une stimulation du sujet sur la base de divers points de déclenchement liés aux seuils des mesures.
PCT/US2013/040357 2012-05-09 2013-05-09 Système et procédé de surveillance vidéo de mouvement, de respiration et de rythme cardiaque sans fixation WO2013170035A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201261644688P 2012-05-09 2012-05-09
US61/644,688 2012-05-09

Publications (1)

Publication Number Publication Date
WO2013170035A1 true WO2013170035A1 (fr) 2013-11-14

Family

ID=49551278

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2013/040357 WO2013170035A1 (fr) 2012-05-09 2013-05-09 Système et procédé de surveillance vidéo de mouvement, de respiration et de rythme cardiaque sans fixation

Country Status (1)

Country Link
WO (1) WO2013170035A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104332022A (zh) * 2014-11-21 2015-02-04 上海斐讯数据通信技术有限公司 一种防止幼儿进食异物的警报系统及方法
EP2977973A1 (fr) 2014-07-21 2016-01-27 Withings Dispositif de surveillance avec capteur de composés organiques volatils et système utilisant celui-ci
CN106308801A (zh) * 2015-06-29 2017-01-11 无锡智感星际科技有限公司 一种利用智能手机检测人体呼吸频率的方法
CN106327790A (zh) * 2016-08-31 2017-01-11 刘哲 基于物联网的智能婴儿防盗系统

Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4409983A (en) * 1981-08-20 1983-10-18 Albert David E Pulse measuring device
US5853005A (en) * 1996-05-02 1998-12-29 The United States Of America As Represented By The Secretary Of The Army Acoustic monitoring system
US6375621B1 (en) * 1987-03-06 2002-04-23 Ocean Laboratories, Inc. Passive apnea monitor
US6491647B1 (en) * 1998-09-23 2002-12-10 Active Signal Technologies, Inc. Physiological sensing device
US20050022606A1 (en) * 2003-07-31 2005-02-03 Partin Dale L. Method for monitoring respiration and heart rate using a fluid-filled bladder
US20090259135A1 (en) * 2008-04-11 2009-10-15 Dymedix Corporation Apparatus and method for creating multiple polarity indicating outputs from two polarized piezoelectric film sensors
US20100152600A1 (en) * 2008-04-03 2010-06-17 Kai Sensors, Inc. Non-contact physiologic motion sensors and methods for use
US7800595B2 (en) * 2003-12-18 2010-09-21 3M Innovative Properties Company Piezoelectric transducer
US20100286607A1 (en) * 2009-05-05 2010-11-11 Saltzstein William E Patient status sensor

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4409983A (en) * 1981-08-20 1983-10-18 Albert David E Pulse measuring device
US6375621B1 (en) * 1987-03-06 2002-04-23 Ocean Laboratories, Inc. Passive apnea monitor
US5853005A (en) * 1996-05-02 1998-12-29 The United States Of America As Represented By The Secretary Of The Army Acoustic monitoring system
US6491647B1 (en) * 1998-09-23 2002-12-10 Active Signal Technologies, Inc. Physiological sensing device
US20050022606A1 (en) * 2003-07-31 2005-02-03 Partin Dale L. Method for monitoring respiration and heart rate using a fluid-filled bladder
US7800595B2 (en) * 2003-12-18 2010-09-21 3M Innovative Properties Company Piezoelectric transducer
US20100152600A1 (en) * 2008-04-03 2010-06-17 Kai Sensors, Inc. Non-contact physiologic motion sensors and methods for use
US20090259135A1 (en) * 2008-04-11 2009-10-15 Dymedix Corporation Apparatus and method for creating multiple polarity indicating outputs from two polarized piezoelectric film sensors
US20100286607A1 (en) * 2009-05-05 2010-11-11 Saltzstein William E Patient status sensor

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2977973A1 (fr) 2014-07-21 2016-01-27 Withings Dispositif de surveillance avec capteur de composés organiques volatils et système utilisant celui-ci
EP2976998A1 (fr) 2014-07-21 2016-01-27 Withings Procédé et dispositif pour surveiller un bébé et pour interaction
EP3321909A1 (fr) 2014-07-21 2018-05-16 Nokia Technologies OY Procédé et dispositif pour surveiller un bébé et pour interaction
US10441178B2 (en) 2014-07-21 2019-10-15 Withings Monitoring device with volatile organic compounds sensor and system using same
CN104332022A (zh) * 2014-11-21 2015-02-04 上海斐讯数据通信技术有限公司 一种防止幼儿进食异物的警报系统及方法
CN104332022B (zh) * 2014-11-21 2017-09-01 上海斐讯数据通信技术有限公司 一种防止幼儿进食异物的警报系统及方法
CN106308801A (zh) * 2015-06-29 2017-01-11 无锡智感星际科技有限公司 一种利用智能手机检测人体呼吸频率的方法
CN106327790A (zh) * 2016-08-31 2017-01-11 刘哲 基于物联网的智能婴儿防盗系统

Similar Documents

Publication Publication Date Title
US20140091945A1 (en) System and method for attachment free motion, respiration, heartbeat, and video monitoring
US20230063373A1 (en) Method and apparatus for monitoring vital signs remotely
WO2019174027A1 (fr) Procédé de surveillance d'informations physiologiques, tapis de surveillance d'informations physiologiques, et matelas
CN108042108B (zh) 一种基于体震信号的睡眠质量监测方法与系统
US5964720A (en) Method and system for monitoring the physiological condition of a patient
US8836516B2 (en) Snoring treatment
US8882677B2 (en) Microphone for remote health sensing
US20100241018A1 (en) Baby monitor
JP5210264B2 (ja) 生体情報を収集し伝達する装置
CN108697390A (zh) 睡眠状态测定装置以及方法、相位相干性计算装置、活体振动信号测定装置，压力状态测定装置以及睡眠状态测定装置以及心跳波形提取方法
US10631739B2 (en) Monitoring vital signs
CN208876492U (zh) 一种生理信息监测垫及床垫
WO2009155593A2 (fr) Système de stéthoscope électronique
JP7297190B2 (ja) 警報発出システム
JP4899117B2 (ja) 心拍・呼吸センサおよびそれを用いた生体監視装置
WO2013170035A1 (fr) Système et procédé de surveillance vidéo de mouvement, de respiration et de rythme cardiaque sans fixation
JP4015115B2 (ja) 小動物用心拍・呼吸数検出機能付き体温保持装置及びそれを用いた小動物用心拍・呼吸数測定システム
TWI418334B (zh) 用於生理訊號及環境訊號感測、分析及回饋之系統
WO2019245055A1 (fr) Tapis pour la détection d'informations biologiques, dispositif pour la détection d'informations biologiques et système pour la distribution d'informations biologiques
JP2020075136A (ja) 生体振動信号検出装置
JP3419732B2 (ja) 密閉空気式音センサーを使用した生体情報収集装置
JP3353460B2 (ja) 監視装置
KR102592050B1 (ko) 소동물용 휴대용 심전도 전극 및 심전도 측정 시스템
JP2001286448A (ja) 密閉空気式音センサーを使用した生体情報収集装置
JP2009082511A (ja) 就寝モニター装置

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 13787792

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 13787792

Country of ref document: EP

Kind code of ref document: A1