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WO1992009232A1 - Detecteur de signes vitaux - Google Patents

Detecteur de signes vitaux Download PDF

Info

Publication number
WO1992009232A1
WO1992009232A1 PCT/US1991/008905 US9108905W WO9209232A1 WO 1992009232 A1 WO1992009232 A1 WO 1992009232A1 US 9108905 W US9108905 W US 9108905W WO 9209232 A1 WO9209232 A1 WO 9209232A1
Authority
WO
WIPO (PCT)
Prior art keywords
individual
output signal
heart
detector
respiration
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/US1991/008905
Other languages
English (en)
Inventor
Harry Herbert Peel, Iii
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
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 Individual filed Critical Individual
Publication of WO1992009232A1 publication Critical patent/WO1992009232A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/024—Measuring pulse rate or heart rate
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B7/00—Instruments for auscultation
    • A61B7/003—Detecting lung or respiration noise

Definitions

  • the present invention relates generally to systems for detecting vital life signs in individuals. More specifically, the present invention provides a method and apparatus for
  • the first step in a medical emergency is to determine whether the heart is beating and breathing is present.
  • the heartbeat is classically found by palpating the pulse in the wrist, neck, or ankle, or by listening to the chest with a stethoscope or ear.
  • Breathing is typically detected by observing motion of the chest and abdomen or sensing airflow through the. nose and mouth. Situations occur, particularly in wartime, in which it is not possible for a human to sensorially detect the pulse or breathing.
  • the vital life sign detector of the present invention overcomes the difficulties of the prior art by providing a system which can be used to determine heart and respiration activity in an individual wearing bulky protective coating.
  • a detector such as an accelerometer or geophone, detects chest wall
  • Hie system of the present invention is contained in a housing which fits comfortably in the gloved hand of medical personnel and requires little dexterity to activate.
  • the housing also has dimensions which allow it to be stable when at rest on the individual, even when the chest surface is at large angles relative to horizontal.
  • the total mass of the device is sufficient to hold the detector effectively stationary relative to the body of the patient.
  • the bottom surface of the housing is covered with a nonslip coating to prevent sliding off the chest.
  • FIG. 1 is an illustration of the vital life sign detector of the present invention placed on an individual.
  • FIG. 2 is a schematic illustration of the signal processing electronics employed in the vital life sign detector of the present invention.
  • FIG. 3a is a graphical representation of an ECG signal produced by an individual.
  • FIG. 3b is a graphical representation of the output signal of the motion detector
  • FIG. 1 is an illustration of the vital life sign detector of the present invention placed on the chest of an immobilized individual 12.
  • the detector 10 is provided with an appropriate display to allow the medical aid personnel 14 to quickly determine whether the individual 12 is alive.
  • the beating of the heart and breathing produce movements and accelerations of the individual's body due to changes in organ volume and momentum transfers. These accelerations and movements can be used to provide an indication of cardiac output and respiratory volume changes.
  • the movements range from very low frequencies (respiration: 0.1 to 0.5 Hz; heart rate: 0.5 to 4 Hz) to relatively high frequencies (breath sounds: 100 to 2000 Hz; heart sounds and Sons: 40 to 1000 Hz). These movements and vibrations normally can be detected with the finger or with the aid of a stethoscope applied to the bare skin.
  • the vibrations and sounds are filtered with the high frequency components that are normally scnsorially detectable being filtered out. It has been observed by the inventor, however, that the low frequency components are attenuated to a far lesser extent and can be sensed with low frequency acceleration measurement devices.
  • the system of the present invention utilizes these low frequency signals to provide an indication of the existence of vital life signs.
  • the vital life sign detector is a small device which, when placed upon a subject, will detect the mechanical vibrations associated with respiratory and heart movement.
  • the device is placed on the chest of the supine casualty.
  • the medical aid provider removes his hand and observes the face of the device.
  • a display - A second display indicates respiratory motion and displays the respiration rate.
  • the chest wall vibrations produced by cardiac and respiratory motions are detected with one or more motion detectors 20, such as an accelerometer or geopho ⁇ e.
  • the motion detectors 20 can use any of a number of transducers, including, but not limited to, piezoelectric, resistive, or electromagnetic. An example of the typical output signal from the motion detector 20 is illustrated in FIG. 3b.
  • the ECG signal is shown in FIG. 3a for reference. It should be noted that there are two pulses associated with each heart beat. These pulses correspond to the onsets of systole and diastole and are synchronous with the first and second heart sounds.
  • the signal from the motion detector 20 is first amplified in an appropriate amplifier 22 and then conditioned in several ways. First, for heart rate, the signal is processed by an analog or digital bandpass filter 24 having a pass band from about 0.5 to about 300 Hz. The transient oscillations are converted and smoothed into a pulse by a pulse shaper circuit 26.. The shaped pulse signal is then fed to a level sensitive, timed, one shot trigger 28 which is held on for approximately 300 msec before resetting.
  • the lock-on time is consistent with the ejection time of the heart. This time lock-on is to prevent double triggering by the second pulse.
  • the timed pulse is then used to turn on the front panel pulse indicator 30 to provide an indication of the existence of cardiac activity.
  • the timed pulse is also fed to a rate computation means 32, which can utilize analog, digital or software rate computing techniques, known in the art, to calculate heart rate.
  • the calculated heart rate is displayed on a front panel display 34. ' to provide a pseudo heart sound output for the user to hear.
  • the transducer signal is passed through a weighted band pass filter 36 which has a transfer function equivalent to that of a stethoscope.
  • This Altered signal is then fed to a suitable power amplifier 38 which is connected to an earphone 40.
  • the earphone is mounted in a stethoscope yoke to facilitate use.
  • the output signal of the motion detector 20 is also provided to a third channel which is used to determine the existence of respiration in the individual by one of several methods.
  • the detector signal is processed in an extremely low bandpass filter 42.
  • the high frequency cutoff of the filter 42 is approximately five Hz.
  • the overall detector and filter low frequency cutoff should be 0.05 Hz or less. It is preferable that
  • the low frequency cutoff be defined by the detector rather than the subsequent electronics.
  • High pass filtering should not be used to avoid long settling times resulting from any large artifacts introduced into the signal.
  • Another suitable method for detecting respiratory movements from the detector signal is to measure the beat-to-beat changes in the intensity of the pulses.
  • the intensity of the pulses are due, in part, to the compliance of the chest within which the heart is beating.
  • the compliance of the chest is dependent upon the volume of air contained within the lungs and the muscle tension of the chest muscle, both of which will change during the course of respiration.
  • the cyclical compliance variations during breathing produce the cyclical variations in the detected pulse amplitudes.
  • the low frequency components produced by filtering methods or the variations in Either signal is also fed to a rate computation means which can utilize analog, digital, or software rate computing techniques, known in the art, to calculate respiration rate.
  • a rate computation means which can utilize analog, digital, or software rate computing techniques, known in the art, to calculate respiration rate.
  • Careful attention to the housing design is required for the detector to operate properly to detect heart beat and respiration through garments.
  • the device should fit comfortably in the gloved hand of medical personnel and should require little dexterity to activate.
  • the housing should have dimensions which allow it to be stable when at rest on the individual, even when the chest surface is at large angles relative to horizontal. The total mass of the device must be sufficient to hold the detector effectively stationary relative to the body of the patient.
  • a rectangular box of 4" x 3" x 1" having a weight of one pound has been found to be a satisfactory upper limit.
  • the bottom surface of the housing should also be covered with a nonslip coating to prevent sliding off the chest.
  • the displays should be large and designed to be easily read especially from low angles relative to the display.
  • the device package should be sealed against contaminants since, as " an emergency device, it will be used in hostile environments.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Public Health (AREA)
  • Molecular Biology (AREA)
  • Veterinary Medicine (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Pathology (AREA)
  • Biophysics (AREA)
  • Physiology (AREA)
  • Pulmonology (AREA)
  • Cardiology (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

Un détecteur de signes vitaux peut être utilisé pour déterminer l'activité cardiaque et respiratoire chez un individu portant des vêtements lourds tels que des vêtements de protection chimique. Un détecteur (20), tel qu'un accéléromètre ou un géophone, détectent les vibrations de la paroi de la poitrine d'un individu et produit un signal de sortie (22) en réponse à ces vibrations. Un signal de sortie est traité pour déterminer l'existence d'une activité cardiaque et respiratoire. Le signal de sortie peut être également traité pour calculer le rythme cardiaque et le rythme respiratoire de l'individu. Le système produit un signal visuel (34) ou un signal audio (40) qui permet au personnel médical de déterminer rapidement si l'individu est vivant.
PCT/US1991/008905 1990-11-27 1991-11-26 Detecteur de signes vitaux Ceased WO1992009232A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US61829790A 1990-11-27 1990-11-27
US618,297 1990-11-27

Publications (1)

Publication Number Publication Date
WO1992009232A1 true WO1992009232A1 (fr) 1992-06-11

Family

ID=24477140

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1991/008905 Ceased WO1992009232A1 (fr) 1990-11-27 1991-11-26 Detecteur de signes vitaux

Country Status (2)

Country Link
AU (1) AU9119991A (fr)
WO (1) WO1992009232A1 (fr)

Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5479932A (en) * 1993-08-16 1996-01-02 Higgins; Joseph Infant health monitoring system
EP0845239A1 (fr) * 1996-11-25 1998-06-03 Pacesetter AB Dispositif médical
WO1998052634A1 (fr) 1997-05-23 1998-11-26 Pa Knowledge Limited Mecanisme d'inhalation
EP0712604A3 (fr) * 1994-11-16 1998-12-02 Pioneer Electronic Corporation Appareil de mesure du rhythme cardiaque
WO1999047044A1 (fr) * 1998-03-20 1999-09-23 Hypertension Diagnostics, Inc. Capteur et procede pour capter la pression arterielle differentielle
US6017313A (en) * 1998-03-20 2000-01-25 Hypertension Diagnostics, Inc. Apparatus and method for blood pressure pulse waveform contour analysis
US6132383A (en) * 1998-03-20 2000-10-17 Hypertension Diagnostics, Inc. Apparatus for holding and positioning an arterial pulse pressure sensor
US6159166A (en) * 1998-03-20 2000-12-12 Hypertension Diagnostics, Inc. Sensor and method for sensing arterial pulse pressure
US6331161B1 (en) 1999-09-10 2001-12-18 Hypertension Diagnostics, Inc Method and apparatus for fabricating a pressure-wave sensor with a leveling support element
WO2003005893A3 (fr) * 2001-07-13 2003-04-03 Isis Innovation Moniteur de la respiration et de la frequence cardiaque
US6733461B2 (en) 2002-08-01 2004-05-11 Hypertension Diagnostics, Inc. Methods and apparatus for measuring arterial compliance, improving pressure calibration, and computing flow from pressure data
DE102004015199A1 (de) * 2004-03-29 2005-10-20 Hartmann Paul Ag Einrichtung zur Erfassung von Vitalitätsfunktionen in einem Kraftfahrzeug
WO2007088539A3 (fr) * 2006-01-31 2008-06-19 Technion Res & Dev Foundation Méthode, dispositif et système pour la surveillance de la ventilation pulmonaire
US20090112078A1 (en) * 2007-10-24 2009-04-30 Joseph Akwo Tabe Embeded advanced force responsive detection platform for monitoring onfield logistics to physiological change
EP2070471A4 (fr) * 2006-09-27 2010-01-20 Univ Cadiz Système de surveillance et d'analyse de signaux cardiorespiratoires et du ronflement
US10052048B2 (en) 2008-05-14 2018-08-21 Koninklijke Philips N.V. Respiratory monitors and monitoring methods
CN113171073A (zh) * 2021-05-18 2021-07-27 南京润楠医疗电子研究院有限公司 一种基于检波器的无感式心率检测方法
US20210251494A1 (en) * 2018-01-26 2021-08-19 Bose Corporation Measuring Respiration with an In-Ear Accelerometer
CN115770021A (zh) * 2021-09-06 2023-03-10 李宗谚 便携式休克检测装置

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4840183A (en) * 1987-08-13 1989-06-20 Tdk Corporation Electrocardiograph
US4972841A (en) * 1988-11-14 1990-11-27 Iguchi Robert K Stethoscope with pulse rate display
US5002060A (en) * 1988-06-16 1991-03-26 Dror Nedivi Medical monitoring system
US5010890A (en) * 1983-08-11 1991-04-30 Vitacomm, Ltd. Vital signs monitoring system
US5025809A (en) * 1989-11-28 1991-06-25 Cardionics, Inc. Recording, digital stethoscope for identifying PCG signatures

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5010890A (en) * 1983-08-11 1991-04-30 Vitacomm, Ltd. Vital signs monitoring system
US4840183A (en) * 1987-08-13 1989-06-20 Tdk Corporation Electrocardiograph
US5002060A (en) * 1988-06-16 1991-03-26 Dror Nedivi Medical monitoring system
US4972841A (en) * 1988-11-14 1990-11-27 Iguchi Robert K Stethoscope with pulse rate display
US5025809A (en) * 1989-11-28 1991-06-25 Cardionics, Inc. Recording, digital stethoscope for identifying PCG signatures

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5479932A (en) * 1993-08-16 1996-01-02 Higgins; Joseph Infant health monitoring system
EP0712604A3 (fr) * 1994-11-16 1998-12-02 Pioneer Electronic Corporation Appareil de mesure du rhythme cardiaque
EP0845239A1 (fr) * 1996-11-25 1998-06-03 Pacesetter AB Dispositif médical
WO1998052634A1 (fr) 1997-05-23 1998-11-26 Pa Knowledge Limited Mecanisme d'inhalation
US6544188B1 (en) 1998-03-20 2003-04-08 Hypertension Diagnostics, Inc. Apparatus and method for holding and positioning an arterial pulse pressure sensor
WO1999047044A1 (fr) * 1998-03-20 1999-09-23 Hypertension Diagnostics, Inc. Capteur et procede pour capter la pression arterielle differentielle
US6017313A (en) * 1998-03-20 2000-01-25 Hypertension Diagnostics, Inc. Apparatus and method for blood pressure pulse waveform contour analysis
US6132383A (en) * 1998-03-20 2000-10-17 Hypertension Diagnostics, Inc. Apparatus for holding and positioning an arterial pulse pressure sensor
US6159166A (en) * 1998-03-20 2000-12-12 Hypertension Diagnostics, Inc. Sensor and method for sensing arterial pulse pressure
US6689069B2 (en) 1998-03-20 2004-02-10 Hypertension Diagnostics, Inc. Apparatus and method for blood pressure pulse waveform contour analysis
US6394958B1 (en) 1998-03-20 2002-05-28 Hypertension Diagnostics, Inc. Apparatus and method for blood pressure pulse waveform contour analysis
US6585659B1 (en) 1999-09-10 2003-07-01 Hypertension Diagnostics, Inc. Pressure-wave sensor with a leveling support element
US6629343B1 (en) 1999-09-10 2003-10-07 Hypertension Diagnostics, Inc. Method for fabricating a pressure-wave sensor with a leveling support element
US6331161B1 (en) 1999-09-10 2001-12-18 Hypertension Diagnostics, Inc Method and apparatus for fabricating a pressure-wave sensor with a leveling support element
WO2003005893A3 (fr) * 2001-07-13 2003-04-03 Isis Innovation Moniteur de la respiration et de la frequence cardiaque
US6733461B2 (en) 2002-08-01 2004-05-11 Hypertension Diagnostics, Inc. Methods and apparatus for measuring arterial compliance, improving pressure calibration, and computing flow from pressure data
DE102004015199A1 (de) * 2004-03-29 2005-10-20 Hartmann Paul Ag Einrichtung zur Erfassung von Vitalitätsfunktionen in einem Kraftfahrzeug
US8226571B2 (en) 2006-01-31 2012-07-24 Amir Landesberg Method device and system for monitoring lung ventilation
WO2007088539A3 (fr) * 2006-01-31 2008-06-19 Technion Res & Dev Foundation Méthode, dispositif et système pour la surveillance de la ventilation pulmonaire
EP2070471A4 (fr) * 2006-09-27 2010-01-20 Univ Cadiz Système de surveillance et d'analyse de signaux cardiorespiratoires et du ronflement
US20090112078A1 (en) * 2007-10-24 2009-04-30 Joseph Akwo Tabe Embeded advanced force responsive detection platform for monitoring onfield logistics to physiological change
US10052048B2 (en) 2008-05-14 2018-08-21 Koninklijke Philips N.V. Respiratory monitors and monitoring methods
US20210251494A1 (en) * 2018-01-26 2021-08-19 Bose Corporation Measuring Respiration with an In-Ear Accelerometer
US12016662B2 (en) * 2018-01-26 2024-06-25 Bose Corporation Measuring respiration with an in-ear accelerometer
CN113171073A (zh) * 2021-05-18 2021-07-27 南京润楠医疗电子研究院有限公司 一种基于检波器的无感式心率检测方法
CN115770021A (zh) * 2021-09-06 2023-03-10 李宗谚 便携式休克检测装置

Also Published As

Publication number Publication date
AU9119991A (en) 1992-06-25

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