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WO1999053277A1 - Detecteur de bruits corporels - Google Patents

Detecteur de bruits corporels Download PDF

Info

Publication number
WO1999053277A1
WO1999053277A1 PCT/IL1998/000172 IL9800172W WO9953277A1 WO 1999053277 A1 WO1999053277 A1 WO 1999053277A1 IL 9800172 W IL9800172 W IL 9800172W WO 9953277 A1 WO9953277 A1 WO 9953277A1
Authority
WO
WIPO (PCT)
Prior art keywords
airbome
sound
primary
membrane
signal
Prior art date
Application number
PCT/IL1998/000172
Other languages
English (en)
Inventor
Noam Gavriely
Maier Fenster
Original Assignee
Karmel Medical Acoustic Technologies, Ltd.
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 Karmel Medical Acoustic Technologies, Ltd. filed Critical Karmel Medical Acoustic Technologies, Ltd.
Priority to AU68509/98A priority Critical patent/AU6850998A/en
Priority to PCT/IL1998/000172 priority patent/WO1999053277A1/fr
Publication of WO1999053277A1 publication Critical patent/WO1999053277A1/fr

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01H—MEASUREMENT OF MECHANICAL VIBRATIONS OR ULTRASONIC, SONIC OR INFRASONIC WAVES
    • G01H11/00—Measuring mechanical vibrations or ultrasonic, sonic or infrasonic waves by detecting changes in electric or magnetic properties
    • G01H11/06—Measuring mechanical vibrations or ultrasonic, sonic or infrasonic waves by detecting changes in electric or magnetic properties by electric means
    • G01H11/08—Measuring mechanical vibrations or ultrasonic, sonic or infrasonic waves by detecting changes in electric or magnetic properties by electric means using piezoelectric devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B7/00—Instruments for auscultation
    • A61B7/02—Stethoscopes
    • A61B7/04—Electric stethoscopes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01H—MEASUREMENT OF MECHANICAL VIBRATIONS OR ULTRASONIC, SONIC OR INFRASONIC WAVES
    • G01H1/00—Measuring characteristics of vibrations in solids by using direct conduction to the detector

Definitions

  • the present invention relates generally to sensors, and specifically to systems suitable for use in body sounds detection and analysis.
  • Auscultation was initially performed by placing the physician's ear directly on the skin of the patient.
  • R.T. Laennec introduced a tool, the stethoscope, for transmitting of body sounds to the ear.
  • stethoscopes include a "chest piece” brought into contact with the patient's skin, and two flexible tubes, terminating in the physician's ears.
  • Swedish patent 8702647-2 to H ⁇ k describes a contact microphone in which the vibrations of the body surface induce deformations of a piezoelectric transducer.
  • Contact sensors using such a piezoelectric element are sensitive to electromagnetic noise caused by nearby AC power lines, by static electricity discharges or by nearby electric devices.
  • sound detecting devices are made to reject shocks and vibrations induced by structure-borne sounds and detect induced by airborne sounds.
  • Devices also exist which are made immune to airborne isotropic sound.
  • a sensor which detects only relative vibrations while rejecting non relative ones is described in US patent 5,456,116 to Lew.
  • the sensor uses a piezoelectric transducer and a mechanical structure to differentiate the vibrations to be detected from those to be rejected.
  • vibrations to be detected are those caused by body sounds.
  • the senor performs at least two measurements, where the relative polarity of the body sounds and the airborne sounds is different in the two measurements.
  • the measurements are performed by transducers.
  • the transducers are piezoelectric elements.
  • the piezoelectric elements are mechanically connected to membranes which vibrate in response to body and airborne sounds.
  • one of the membranes is in contact with the body.
  • the membranes preferably metallic, are mechanically coupled to each other, preferably by a gas or liquid.
  • the output of transducers are combined, preferably by a differential amplifier, so that the airborne sounds are at least partly canceled.
  • airborne sound reaches one of the membranes directly from surroundings, and reaches the other membrane through the body.
  • the amplitude response to airborne sounds of the membrane receiving such sounds directly is adjusted so as to be as close as possible to the amplitude response to airborne sounds of the membrane in contact with the body.
  • the adjustment of the amplitude response is made by mechanically loading the membrane facing the air, preferably by coating the membrane with a thin layer of a substance.
  • the amplitude response adjustment is made by an electrical trimmer and/or by utilizing weighted combination of the amplitude response of the two membranes when combining the outputs of the elements.
  • the amplitude response adjustment is automatically performed to calibrate the sensor.
  • a device for detecting sounds generated within a body comprising:
  • a primary sensor placed on the body which receives first sound vibrations caused by the sounds generated within the body and second sound vibrations caused by airborne sound and which generates a primary electrical sensor signal in response thereto comprised of first and second portions, in a first ratio, responsive to said first and second sound vibrations respectively; and airborne sound cancellation circuitry which receives the first signal and produces an output signal comprised of first and second portions, in a second ratio higher than said first ratio, responsive to said first and second sound vibrations respectively.
  • the second portion of said primary sensor signal is responsive to airborne sound which travels to said first sensor via said body.
  • the device includes a secondary sensor which receives airborne sound and produces a secondary sensor signal wherein said airborne sound cancellation circuitry utilizes said secondary sensor signal to produce said output signal.
  • the secondary sensor signal comprises first and second portions responsive to said sounds generated within the body and said airborne sounds.
  • the cancellation circuitry combines a signal derived from the secondary sensor signal with a signal derived from the primary sensor signal in forming said output signal.
  • the cancellation circuitry comprises an equalizer which adjusts the amplitude of at least one of the primary sensor and secondary sensor signals to increase said second ratio.
  • equalizer provides a frequency dependent adjustment to at least one of the primary and secondary signals.
  • the equalizer provides a frequency independent adjustment to at least one of the primary and secondary signals.
  • the device includes equalizer adjustment • circuitry which, in a calibration mode adjusts the equalizer to reduce the second portion of the output signal in response to an airborne sound.
  • the device a sound generator which, during the calibration mode, produces an airborne sound and wherein said adjustment circuitry adjusts said equalizer circuitry to reduce the response of the device to a minimum value.
  • the thus produced airborne sound is essentially a single frequency sound.
  • the sound generator produces airborne sound at a plurality of frequencies in said calibration mode.
  • the primary sensor comprises a primary membrane and a primary transducer and the primary transducer produces said primary sensor output responsive to deformations of the primary membrane.
  • the primary transducer is a piezoelectric element.
  • the secondary sensor comprises a secondary membrane and a secondary transducer and the secondary transducer produces said secondary sensor output responsive to deformations of the secondary membrane.
  • the secondary transducer is a piezoelectric element.
  • the secondary membrane is displaced from the first membrane.
  • the secondary membrane is coated with a material to reduce the response of the secondary sensor to airborne signals.
  • the secondary member is coated with a membrane having a response similar to that of the human skin.
  • the secondary membrane is of a different thickness than the first membrane to reduce the response of the secondary sensor to airborne signals.
  • the first and second sensors are mechanically or acoustically coupled such that vibrations of said primary membrane cause vibrations of the secondary membrane.
  • the coupling comprises a closed volume of gas or liquid and the primary and secondary membranes each form portions of an enclosure of the volume.
  • the membrane is a metallic membrane.
  • a device for measurement of sounds conducted from the interior of the body to its surface in the presence of airborne sounds conducted through the body comprising: a primary sensor comprises a primary membrane and a primary transducer, wherein the primary transducer produces a primary sensor output signal responsive to deformations of the primary membrane; a secondary sensor comprising a secondary membrane and a secondary transducer, wherein the secondary transducer produces a secondary sensor output signal responsive to deformations of the secondary membrane; and airborne sound cancellation circuitry which combines a signal derived from said secondary sensor output signal from a said primary output signal to produce an output signal having a reduced component responsive to the airborne sound.
  • the cancellation circuitry comprises an equalizer which adjusts the amplitude of at least one of the primary sensor and secondary sensor signals to reduce the component responsive to the airbome sound.
  • the equalizer provides a frequency dependent adjustment to at least one of the primary and secondary signals.
  • the equalizer provides a frequency independent adjustment to at least one of the primary and secondary signals.
  • the device includes equalizer adjustment circuitry which, in a calibration mode adjusts the equalizer to reduce the second portion of the output signal in response to an airbome sound.
  • the device includes a sound generator which, during the calibration mode, produces an airbome sound and wherein said adjustment circuitry adjusts said equalizer circuitry to reduce the response of the device to a minimum value.
  • the thus produced airbome sound is essentially a single frequency sound.
  • the sound generator produces airbome sound at a plurality of frequencies in said calibration mode.
  • a method of reducing the effect of airbome sound on a measurement of sounds produced in a body and measured at the surface thereof comprising: providing a signal responsive to sound produced in the body and measured at the surface of the body and contaminated by a signal responsive to said airbome sounds; providing a second signal having at least a component responsive to said airbome sounds; and processing the first signal utilizing the second signal to produce an output signal having a reduced the relative amplitude of the signal responsive to airbome sounds.
  • providing a second signal comprises providing a second signal having a component responsive to sound produced in the body wherein the relative polarity of the signals responsive to the airbome and body produced sound is reversed for the second signal as compared to the first signal.
  • the method includes adjusting at least one of the first and second signals to further reduce the relative amplitude of the signal responsive to the airbome sounds.
  • the adjustment is determined during a calibration stage comprising: placing a device providing the first and second signals on the body in a position at which such measurement is to be made; providing an airbome audio signal; adjusting at least one of the first and second signals to minimize the response of the output signal to said provided airbome signal; and utilizing said adjustment when measuring body sounds.
  • the adjustment is frequency insensitive.
  • the adjustment varies with frequency.
  • FIG. 1 schematically shows the logic of operation and a cross-sectional view of the construction of a sensor, in accordance with a preferred embodiment of the present invention
  • Fig. 2 schematically shows a cross-sectional view of the construction of a sensor in accordance with an alternative preferred embodiment of the invention and a preferred method of mounting the sensor.
  • FIG. 1 schematically depicts the logic of a sensor 6 in accordance with a preferred embodiment of the present invention.
  • Sensor 6 comprises a pair of membranes 10 and 12, a ' pair of transducers 14 and 16, a combiner 18 and a housing 42 to which the membranes 10 and 12 are attached.
  • a gas or liquid 22 fills enclosure 20 and mechanically couples membranes 10 and 12. Use of different gases or liquids 22 will result in different mechanical coupling of membranes 10 and 12. When vibrating, membranes 10 and 12 transfer their vibrational energy to transducers
  • Transducers 14 and 16 transform this energy into another form, preferably electrical energy.
  • Outputs 30 and 32 of transducers 14 and 16 are combined by combiner 18 and extracted from sensor 6 as a final output 40.
  • Membranes and surfaces vibrate whenever sound or vibrations reach them, as for example surfaces 24 of a body 26 under the influence of body sounds 28 created inside body 26.
  • the surface of membrane 10 is brought into contact with surface 24.
  • Fig. 1 the contact of membrane 10 and surface 24 is not shown in Fig. 1, however, they are shown in contact in Fig. 2 which is shows an alternative preferred embodiment of the invention.
  • Vibrations induced by body sounds 28 which reach surface 24 are transmitted to membrane 10 by physical contact and then, through coupling medium 22, to membrane 12 arrow (arrow IV).
  • Airbome sounds 34 such as speech, are transmitted directly to membrane 12 (arrow V) and through body 26 (arrows VI, VII) to membrane 10.
  • the relative polarity of body and airbome vibrations received by membrane 10 is different from the relative polarity of those vibrations received by membrane 12 (arrows IV and V).
  • Combiner 18 combines outputs 30 and 32 so as to subtract the portion of the output generated by airbome sound 34 which reaches membranes 10, 12, and to add the portion of the output generated by body sounds 28.
  • the amplitude of vibrations induced by airborne sound 34 in membrane 12 is controlled, as to match it as closely as possible to the amplitude of vibrations induced by airbome sound 34 in membrane 10 so that the amplitude response of the two transducers to airbome sounds is substantially the same.
  • Airbome sound which may reach membrane 10 through the coupling medium does not affect the proper operation of a sensor built in accordance with this embodiment, because the amplitude of vibrations induced by airbome sound 34 in membrane 12 is matched as closely as possible to the algebraic sum of the amplitudes of airbome sound received at membrane 10 through the body and through coupling medium.
  • the efficiency of coupling medium 22 does not affect the proper operation of a sensor built in accordance with this embodiment, because, even if no body sound 28 can reach membrane 12, cancellation of airbome sound in ' accordance with the above, will still be performed by controlling the amplitude of vibrations induced by airbome sound in membrane 12, with no dependence on relative polarity of sounds detected by membranes 10 and 12.
  • the amplitude of vibrations induced by airbome sound in membranes 10 and 12 is obtained by contacting membrane 12 with substance 36 which alters its amplitude response, preferably matching its response to that of the human skin. Alternatively or additionally, the response is altered by putting some distributed weights, (not shown), on the membrane. Alternatively or additionally, airbome sound 34 which reaches membranes 10, 12 in different directions, is electronically canceled by
  • Membranes 10 and 12 preferably are thin metallic sheets made of stainless steel, preferably between 200 and 250 microns thick.
  • the membranes are preferably conductively glued to transducers 14 and 16 and, at contact points 48, to a preferably conductive sensor housing 42.
  • Transducers 14 and 16 are preferably piezoelectric crystals (PZT) although other transducers such as optical transducers may be used.
  • Inner faces 52 and 54, of PZTs 14 and 16 are respectively conductively connected to output wires 30A and 32 A, while sensor housing 42 is grounded through wire 32B at contact point 50. Thus, the outer faces of transducers 14 and 16 are also grounded.
  • the part of outputs 30 and 32 related to airbome sounds 34 are canceled by differential amplifier 18, while the part related to body sounds 28 is extracted as final output 40.
  • the output of transducer 16 is additionally ' fed to a second operational amplifier (not shown), for use by breath sound equipment as an ambient noise detector.
  • the amplitude of vibrations induced by airbome sounds 34 in membrane 12 is matched to that induced in membrane 10 by contacting it with a substance 36, preferably by coating or pasting a thin layer on membrane 12. It has been found that a closed cell foam tape such as 3M type 1772 Foam Medical Tape with a thickness of 1.2 mm is suitable. Alternatively or additionally, in some preferred embodiments, electronic adjustment of the amplitude of signals 30 and 32 is used. In these embodiments, trimmer 46 is adjusted to match the amplitude of the outputs of transducers 14 and 16 to airbome sounds.
  • the transducer 16 may be calibrated, in situ, to provide optimum cancellation of airbome sounds.
  • airbome sound is generated. This sound may be speech or other sound. Trimmer 46 or the relative gain of the channels of combiner 18 are varied to provide minimum signal, at 40, from such sounds.
  • a servo controlled equalizer is used to equalize, at predetermined frequencies of the audio spectrum, the part of outputs 30 and 32 generated by airbome sounds.
  • airbome sound preferably at individual frequencies is generated, preferably corresponding to the center frequencies of bands of the equalizer.
  • Circuitry receives the outputs generated in response to sound at the individual frequencies and changes the respective channel transmission of the equalizer until the output at 40 is minimized or eliminated.
  • Fig. 2 shows a sensor, in accordance with an alternative preferred embodiment of the invention, in which housing 42 is formed of a plastic material.
  • membranes separate connection is preferably made to the outside surfaces of transducers 14 and 16, preferably via membranes 10 and 12.
  • epoxy 48' need not be conductive.
  • Fig. 2 also illustrates a preferred method of attaching the sensors of Figs. 1 or 2.
  • the sensor is surrounded by a sponge holding fixture 100 (which may be of the same material as forms the layer 36 of Fig. 1).
  • the height of fixture 100 may be the same as or slightly less than that of housing 42.
  • fixture 42 is formed with a slit to allow for the easy removal of the sensor output cable shield 38 and the wires it contains.
  • Fixture 100 is " further formed with a sticky surface where it touches the skin of the subject such that it is securely, but removably attached thereto.
  • a layer 102 of tape is preferably used to secure the fixture to the sensor.
  • tape 102 is of the same material as described above with respect to the preferred embodiment of layer 36 of Fig. 1.
  • tape 102 provides the double function of securing the sensor and providing the desired loading of membrane 12.

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  • Physics & Mathematics (AREA)
  • General Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of Mechanical Vibrations Or Ultrasonic Waves (AREA)

Abstract

L'invention concerne un dispositif permettant de détecter les sons générés à l'intérieur du corps. Ce dispositif comprend (1) un capteur primaire placé sur la corps, qui reçoit de premières vibrations sonores causées par les sons générés à l'intérieur du corps et de secondes vibrations causées par le son aérien, et génère un signal électrique de détecteur primaire en réponse à ces vibrations, ce signal comportant une première et une seconde portion à raison d'un premier rapport, en fonction respectivement des premières et des secondes vibrations sonores; et (2) des circuits d'élimination des sons aériens qui reçoivent le premier signal et produisent un signal de sortie comprenant une première et une seconde portion à raison d'un second rapport plus élevé que le premier rapport et dépendant respectivement des premières et des secondes vibrations sonores.
PCT/IL1998/000172 1998-04-08 1998-04-08 Detecteur de bruits corporels WO1999053277A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
AU68509/98A AU6850998A (en) 1998-04-08 1998-04-08 Sensor for body sounds
PCT/IL1998/000172 WO1999053277A1 (fr) 1998-04-08 1998-04-08 Detecteur de bruits corporels

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/IL1998/000172 WO1999053277A1 (fr) 1998-04-08 1998-04-08 Detecteur de bruits corporels

Publications (1)

Publication Number Publication Date
WO1999053277A1 true WO1999053277A1 (fr) 1999-10-21

Family

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IL1998/000172 WO1999053277A1 (fr) 1998-04-08 1998-04-08 Detecteur de bruits corporels

Country Status (2)

Country Link
AU (1) AU6850998A (fr)
WO (1) WO1999053277A1 (fr)

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6661161B1 (en) 2002-06-27 2003-12-09 Andromed Inc. Piezoelectric biological sound monitor with printed circuit board
EP1292229A4 (fr) * 2000-06-22 2005-03-23 Au Ct Advanced Med Technology Capteur biophysique
US6942890B1 (en) * 1998-12-23 2005-09-13 Jan Van Buuren Fortification of food products with olive fruit ingredients
EP1519165A3 (fr) * 2003-09-29 2006-04-05 Hosiden Corporation Capteur de vibrations piézoélectrique
AU2001265701B2 (en) * 2000-06-22 2006-07-27 Australian Centre For Advanced Medical Technology Ltd Biophysical sensor
US7998091B2 (en) 2005-11-23 2011-08-16 3M Innovative Properties Company Weighted bioacoustic sensor and method of using same
US20110213273A1 (en) * 2009-10-15 2011-09-01 Telfort Valery G Acoustic respiratory monitoring sensor having multiple sensing elements
US8024974B2 (en) 2005-11-23 2011-09-27 3M Innovative Properties Company Cantilevered bioacoustic sensor and method using same
US8523781B2 (en) 2009-10-15 2013-09-03 Masimo Corporation Bidirectional physiological information display
WO2013132012A1 (fr) * 2012-03-07 2013-09-12 Computerized Medical Technology In Sweden Ab Capteur et stéthoscope
US8870792B2 (en) 2009-10-15 2014-10-28 Masimo Corporation Physiological acoustic monitoring system
US9028429B2 (en) 2008-12-30 2015-05-12 Masimo Corporation Acoustic sensor assembly
US9066680B1 (en) 2009-10-15 2015-06-30 Masimo Corporation System for determining confidence in respiratory rate measurements
US9106038B2 (en) 2009-10-15 2015-08-11 Masimo Corporation Pulse oximetry system with low noise cable hub
US9107625B2 (en) 2008-05-05 2015-08-18 Masimo Corporation Pulse oximetry system with electrical decoupling circuitry
US9192351B1 (en) 2011-07-22 2015-11-24 Masimo Corporation Acoustic respiratory monitoring sensor with probe-off detection
US9307928B1 (en) 2010-03-30 2016-04-12 Masimo Corporation Plethysmographic respiration processor
US9386961B2 (en) 2009-10-15 2016-07-12 Masimo Corporation Physiological acoustic monitoring system
US9724016B1 (en) 2009-10-16 2017-08-08 Masimo Corp. Respiration processor
US9782110B2 (en) 2010-06-02 2017-10-10 Masimo Corporation Opticoustic sensor
US9955937B2 (en) 2012-09-20 2018-05-01 Masimo Corporation Acoustic patient sensor coupler
US10441181B1 (en) 2013-03-13 2019-10-15 Masimo Corporation Acoustic pulse and respiration monitoring system
US10463340B2 (en) 2009-10-15 2019-11-05 Masimo Corporation Acoustic respiratory monitoring systems and methods
US20200178923A1 (en) * 2009-10-15 2020-06-11 Masimo Corporation Acoustic respiratory monitoring systems and methods
US10729402B2 (en) 2009-12-04 2020-08-04 Masimo Corporation Calibration for multi-stage physiological monitors
US10828007B1 (en) 2013-10-11 2020-11-10 Masimo Corporation Acoustic sensor with attachment portion

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3832762A (en) * 1972-05-22 1974-09-03 Texas Instruments Inc Method of producing a matched parameter acceleration cancelling hydrophone
US3970878A (en) * 1975-03-31 1976-07-20 Teledyne Exploration Company Piezoelectric transducer unit and hydrophone assembly
US4301809A (en) * 1980-03-13 1981-11-24 Pinchak Alfred C Esophageal monitoring apparatus
WO1995014845A1 (fr) * 1993-11-23 1995-06-01 Den Norske Stats Oljeselskap A.S Systeme a transducteur
US5539831A (en) * 1993-08-16 1996-07-23 The University Of Mississippi Active noise control stethoscope
WO1997025598A1 (fr) * 1996-01-08 1997-07-17 Sagem S.A. Capteur de vibrations
US5812678A (en) * 1996-02-26 1998-09-22 Scalise; Stanley J. Auscultation augmentation device

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3832762A (en) * 1972-05-22 1974-09-03 Texas Instruments Inc Method of producing a matched parameter acceleration cancelling hydrophone
US3970878A (en) * 1975-03-31 1976-07-20 Teledyne Exploration Company Piezoelectric transducer unit and hydrophone assembly
US4301809A (en) * 1980-03-13 1981-11-24 Pinchak Alfred C Esophageal monitoring apparatus
US5539831A (en) * 1993-08-16 1996-07-23 The University Of Mississippi Active noise control stethoscope
WO1995014845A1 (fr) * 1993-11-23 1995-06-01 Den Norske Stats Oljeselskap A.S Systeme a transducteur
WO1997025598A1 (fr) * 1996-01-08 1997-07-17 Sagem S.A. Capteur de vibrations
US5812678A (en) * 1996-02-26 1998-09-22 Scalise; Stanley J. Auscultation augmentation device

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
ZUCKERWAR A J ET AL: "DEVELOPMENT OF A PIEZOPOLYMER PRESSURE SENSOR FOR A PORTABLE FETAL HEART RATE MONITOR", IEEE TRANSACTIONS ON BIOMEDICAL ENGINEERING, vol. 40, no. 9, 1 September 1993 (1993-09-01), pages 963 - 969, XP000448110 *

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US6942890B1 (en) * 1998-12-23 2005-09-13 Jan Van Buuren Fortification of food products with olive fruit ingredients
AU2001265701B2 (en) * 2000-06-22 2006-07-27 Australian Centre For Advanced Medical Technology Ltd Biophysical sensor
EP1292229A4 (fr) * 2000-06-22 2005-03-23 Au Ct Advanced Med Technology Capteur biophysique
US6988993B2 (en) 2000-06-22 2006-01-24 Australian Centre For Advanced Medical Technology Ltd. Biophysical sensor
US6661161B1 (en) 2002-06-27 2003-12-09 Andromed Inc. Piezoelectric biological sound monitor with printed circuit board
EP1519165A3 (fr) * 2003-09-29 2006-04-05 Hosiden Corporation Capteur de vibrations piézoélectrique
US7998091B2 (en) 2005-11-23 2011-08-16 3M Innovative Properties Company Weighted bioacoustic sensor and method of using same
US8024974B2 (en) 2005-11-23 2011-09-27 3M Innovative Properties Company Cantilevered bioacoustic sensor and method using same
US8333718B2 (en) 2005-11-23 2012-12-18 3M Innovative Properties Company Weighted bioacoustic sensor and method of using same
US11412964B2 (en) 2008-05-05 2022-08-16 Masimo Corporation Pulse oximetry system with electrical decoupling circuitry
US9107625B2 (en) 2008-05-05 2015-08-18 Masimo Corporation Pulse oximetry system with electrical decoupling circuitry
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US12419588B2 (en) 2009-10-15 2025-09-23 Masimo Corporation System and method for monitoring respiratory rate measurements
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