WO1992009232A1 - Vital life sign detector - Google Patents

Vital life sign detector Download PDF

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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
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WO
WIPO (PCT)
Prior art keywords
individual
output signal
heart
detector
respiration
Prior art date
Application number
PCT/US1991/008905
Other languages
French (fr)
Inventor
Harry Herbert Peel, Iii
Original Assignee
Harry Herbert Peel, Iii
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 Harry Herbert Peel, Iii filed Critical Harry Herbert Peel, Iii
Publication of WO1992009232A1 publication Critical patent/WO1992009232A1/en

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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—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, 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 pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/024—Detecting, measuring or recording 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—Detecting, measuring or recording 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—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • 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.

Abstract

A vital life sign detector which can be used to determine heart and respiration activity in an individual wearing bulky clothing, such as chemical warfare protective clothing. A detector (20), such as an accelerometer or geophone, detects chest wall vibrations of an individual and produces an output signal (22) in response thereto. The output signal is processed to determine the existence of cardiac and respiratory activity. The output signal can be further processed to calculate the heart rate and respiration rate of the individual. The system produces a visual (34) or audio signal (40) which allows medical personnel to determine quickly whether the individual is alive.

Description

VITAL LIFE SIGN DETECTOR
Held of the Invention 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
detecting vital life signs, such as heart rate and respiration, in an individual wearing heavy garments or other covering. An example of such an individual would be a soldier wearing arctic clothing or chemical warfare protective gear. Background of the Invention 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. This is particularly true during arctic or chemical warfare where the casualty and the medical personnel may be completely encased in heavy clothing and may be wearing heavy gloves or masks. Blood loss, shock, and trauma may also reduce the intensity of the pulse and respiration which make sensory detection of vital life signs difficult and time consuming. In situations where large numbers of casualties are present, it is important that care ' determining the presence of a pulse and breathing-is, therefore, a central issue in casualty management. The prior art has heretofore failed to provide a system for quickly detecting vital life signs in individuals, such as wartime casualties, who arc wearing bulky protective
clothing. The vital life sign detector of the present invention, described in greater detail
below, fulfills this need.
the Invention 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. In the preferred embodiment of the invention, a detector, such as an accelerometer or geophone, detects chest wall
vibrations of an individual and produces an output signal in response thereto. The output signal is processed to determine the existence of cardiac and respiratory activity. The output signal can be further processed to calculate the heart rate and respiration rate of the individual. Numerous types of transducers can be used to detect the chest wall vibrations, including piezoelectric, electromagnetic and resistive transducers. 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.
of the Drawings 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
employed in the present invention.
the Preferred Embodiment
_ 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 bruits: 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. However, when clothing or other coupling materials are introduced between the skin and human sensor, 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.
In summary, 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. Typically, 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. As shown schematically in FIG. 2, the chest wall vibrations produced by cardiac and respiratory motions are detected with one or more motion detectors 20, such as an accelerometer or geophoπe. 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. To provide this signal, 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. In the preferred embodiment of the invention, 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. In one method, 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. 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. Finally, the device package should be sealed against contaminants since, as" an emergency device, it will be used in hostile environments. Although the vital life sign detector of the present invention has been described in connection with the preferred embodiment, it is not intended to be limited to the specific form set forth herein, but on the contrary, it is intended to cover such modifications, alternatives, and equivalents as can be reasonably included within the spirit and scope of the invention as defined by the appended claims.

Claims

m for detecting vital life signs in an individual, comprising: means for detecting vibrations in the chest wall of an individual and for producing an output signal in response thereto, even when said individual is wearing bulky clothing; means for correlating said output signal with vital life signs of said individual.
vibrations comprising a piezoelectric transducer.
3. The system according to claim 1, said means for detecting said chest wall vibrations comprising a electromagnetic transducer.
4. The system according to claim 1, said means for detecting said chest wall vibrations comprising a resistive transducer.
5. The system according to claim 1, further comprising means for processing said output signal to provide an indication of heart sounds produced by said individual.
6. The system according to claim 5, further comprising means for using said heart sounds to calculate the heart rate of said individual.
7. The system according to claim 6, further comprising a weighted bandpass filter for processing said output signal, said weighted bandpass filter having a transfer function equivalent to that of a stethoscope to provide an electrical signal representation of audible heart sounds, and an audio signal transducer to convert said electrical representation into an audible heart sound. said output signal to determine the existence of respiration in said individual.
9. The system according to claim 8, further comprising means for calculating the respiration rate of said individual.
10. The system according to claim 1, said system being contained in a housing having sufficient mass to maintain said detector in an effectively stationary position relative to the body of said individual.
A vital life sign detector which can be used to dctermine heart and respiration activity in an individual wearing bulky clothing, such as chemical warfare protective clothing. A detector, such as an accelerometer or geophone, detects chest wall vibrations of an individual and produces an output signal in response thereto. Hie output signal is processed to determine the existence of cardiac and respiratory activity. The output signal can be further processed to calculate the heart rate and respiration rate of the individual. The system produces a visual or audio signal which allows medical personnel to determine quickly whether the individual is alive.
PCT/US1991/008905 1990-11-27 1991-11-26 Vital life sign detector WO1992009232A1 (en)

Applications Claiming Priority (2)

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

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Cited By (18)

* 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
EP0712604A2 (en) * 1994-11-16 1996-05-22 Pioneer Electronic Corporation Cardiac rate measuring apparatus
EP0845239A1 (en) * 1996-11-25 1998-06-03 Pacesetter AB Medical device
WO1998052634A1 (en) 1997-05-23 1998-11-26 Pa Knowledge Limited Inhaler mechanism
WO1999047044A1 (en) * 1998-03-20 1999-09-23 Hypertension Diagnostics, Inc. Sensor and method for sensing arterial pulse pressure
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
WO2003005893A2 (en) * 2001-07-13 2003-01-23 Isis Innovation Limited Respiration and heart rate monitor
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 (en) * 2004-03-29 2005-10-20 Hartmann Paul Ag Device for determining the vital functions of a person in motor vehicle using ultrasound comprises an ultrasound transmitter and receiver arranged in passenger restraint system so that they lie in lower abdominal region of the person
WO2007088539A3 (en) * 2006-01-31 2008-06-19 Technion Res & Dev Foundation Method device and system for monitoring lung ventilation
US20090112078A1 (en) * 2007-10-24 2009-04-30 Joseph Akwo Tabe Embeded advanced force responsive detection platform for monitoring onfield logistics to physiological change
EP2070471A1 (en) * 2006-09-27 2009-06-17 Universidad de Cadiz System for monitoring and analysing cardiorespiratory signals and snoring
US10052048B2 (en) 2008-05-14 2018-08-21 Koninklijke Philips N.V. Respiratory monitors and monitoring methods
CN113171073A (en) * 2021-05-18 2021-07-27 南京润楠医疗电子研究院有限公司 Non-inductive heart rate detection method based on detector
US20210251494A1 (en) * 2018-01-26 2021-08-19 Bose Corporation Measuring Respiration with an In-Ear Accelerometer

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Cited By (27)

* 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
EP0712604A2 (en) * 1994-11-16 1996-05-22 Pioneer Electronic Corporation Cardiac rate measuring apparatus
EP0712604A3 (en) * 1994-11-16 1998-12-02 Pioneer Electronic Corporation Cardiac rate measuring apparatus
EP0845239A1 (en) * 1996-11-25 1998-06-03 Pacesetter AB Medical device
WO1998052634A1 (en) 1997-05-23 1998-11-26 Pa Knowledge Limited Inhaler mechanism
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
US6394958B1 (en) 1998-03-20 2002-05-28 Hypertension Diagnostics, Inc. Apparatus and method for blood pressure pulse waveform contour analysis
US6689069B2 (en) 1998-03-20 2004-02-10 Hypertension Diagnostics, Inc. Apparatus and method for blood pressure pulse waveform contour analysis
WO1999047044A1 (en) * 1998-03-20 1999-09-23 Hypertension Diagnostics, Inc. Sensor and method for sensing arterial pulse pressure
US6544188B1 (en) 1998-03-20 2003-04-08 Hypertension Diagnostics, Inc. Apparatus and method for holding and positioning an arterial pulse pressure sensor
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
US6585659B1 (en) 1999-09-10 2003-07-01 Hypertension Diagnostics, Inc. Pressure-wave sensor with a leveling support element
WO2003005893A3 (en) * 2001-07-13 2003-04-03 Isis Innovation Respiration and heart rate monitor
WO2003005893A2 (en) * 2001-07-13 2003-01-23 Isis Innovation Limited Respiration and heart rate monitor
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 (en) * 2004-03-29 2005-10-20 Hartmann Paul Ag Device for determining the vital functions of a person in motor vehicle using ultrasound comprises an ultrasound transmitter and receiver arranged in passenger restraint system so that they lie in lower abdominal region of the person
WO2007088539A3 (en) * 2006-01-31 2008-06-19 Technion Res & Dev Foundation Method device and system for monitoring lung ventilation
US8226571B2 (en) 2006-01-31 2012-07-24 Amir Landesberg Method device and system for monitoring lung ventilation
EP2070471A1 (en) * 2006-09-27 2009-06-17 Universidad de Cadiz System for monitoring and analysing cardiorespiratory signals and snoring
EP2070471A4 (en) * 2006-09-27 2010-01-20 Univ Cadiz System for monitoring and analysing cardiorespiratory signals and snoring
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
CN113171073A (en) * 2021-05-18 2021-07-27 南京润楠医疗电子研究院有限公司 Non-inductive heart rate detection method based on detector

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