US3905354A - Blood pressure measuring system - Google Patents

Blood pressure measuring system Download PDF

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Publication number
US3905354A
US3905354A US443442A US44344274A US3905354A US 3905354 A US3905354 A US 3905354A US 443442 A US443442 A US 443442A US 44344274 A US44344274 A US 44344274A US 3905354 A US3905354 A US 3905354A
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Prior art keywords
pressure
signals
pulses
patient
acoustic
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Expired - Lifetime
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US443442A
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English (en)
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Abraham Lichowsky
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Medical Monitors Inc
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Medical Monitors Inc
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Priority to US443442A priority Critical patent/US3905354A/en
Priority to CA219,946A priority patent/CA1005563A/en
Priority to GB593475A priority patent/GB1460413A/en
Priority to DE19752506651 priority patent/DE2506651A1/de
Priority to JP50019496A priority patent/JPS50118588A/ja
Priority to FR7505046A priority patent/FR2260975A1/fr
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Publication of US3905354A publication Critical patent/US3905354A/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/02208—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers using the Korotkoff method
    • 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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/02141—Details of apparatus construction, e.g. pump units or housings therefor, cuff pressurising systems, arrangements of fluid conduits or circuits
    • 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
    • A61B7/045—Detection of Korotkoff sounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7239—Details of waveform analysis using differentiation including higher order derivatives

Definitions

  • the blood pressure measuring system includes the generation of output signals by correlation of pressure pulses detected in a fluid system used to close off the blood flow, with acoustic pulses detected downstream near the blood flow close-off point in a patients arm or other portion of his body. Correlating the pressure pulses with the acoustic pulses and generating output signals only when there is a coincidence between the pressure and acoustic pulses minimizes the effect of spurious signals and artifacts to the end that a more accurate systolic and diastolic blood pressure reading may be provided.
  • the systolic pressure is indicated at the point in time that the output signals start and the diastolic pressure is indicated at the point in time that the output signals terminate.
  • This invention relates to blood pressure measuring systems and more particularly to an improved system for automatically indicating and/or recording a patients systolic and diastolic blood pressures by the use of pneumatic and electronic components so that it is no longer necessary for a doctor or nurse to conduct the various steps involved in determining such pressures.
  • the systolic blood pressure of a patient or person is a measure of the peak or maximum pressure in the patients circulatory system whereas the diastolic blood pressure is a measure of the average pressure of blood flowing through the circulatory system.
  • the conventional and normal procedure for determining these pressures involves a doctor or nurse closing off a portion of the patients circulatory system, such as at the patients arm to block flow of blood to the lower por tion of the arm.
  • a fluid pressure chamber normally operated by air is wrapped about the upper portion of the patients arm and pressure is applied until the blood flow is cut off.
  • the doctor can determine when sufficient pressure has been applied to close off the blood flow, there being an absence of acoustic pulses'resulting from blood pressure and flow pulses detected in the stethoscope.
  • the doctor or nurse will gradually release the pressure and carefully listen with the stethoscope for the start of blood flow to the lower portion of the arm.
  • a first acoustic pulse is detected in the stethoscope, a reading of a suitable manometer or other pressure indicating device connected to the fluid chamber is taken, thereby indicating the systolic blood pressure.
  • the pressure is gradually decreased further until such time as there is an absence of pronounced acoustic pulses detected by the doctor listening in the stethoscope and at this point, another pressure reading is taken, which serves to indicate the diastolic blood pressure.
  • the acoustic pulses are divided into five phases based on changes in the characteristics of the sounds as cuff pressure is decreased.
  • Phase IV is a muffled sound relative to the first three phases.
  • Phase V is silent. There is some disagreement on whether the end of Phase III or Phase IV more accurately represents the true diastolic pressure.
  • the present invention contemplates a system for automatically measuring a patients systolic and diastolic blood pressure wherein most extraneous noises and spurious signals are eliminated all to the end that great accuracy is achieved in a fully automatic manner.
  • the system involves applying pressure to close off blood flow to a portion of the patient.
  • the ap plied pressure is then decreased gradually and then pressure pulses are detected corresponding to the' patients heartbeat and blood flow pulses in the closed off portion.
  • acoustic pulses are detected in aporti o'n of the patient downstream of the blood flow as the applied pressure is being decreased.
  • Electrical signals in turn are generated corresponding to thedetected pressure and acoustic pulses. These signals are then quantized and correlated to provide an output signal only when a pressure signal occurs simultaneously with an acoustic signal.
  • Spurious signals or extraneous pulses are thus substantially eliminated, since most disturbances causing pressure fluctuations do not produce significant acoustic output while acoustic interference does not produce significant pressure transients.
  • heartbeats within the appropriate cuff pressure range produce pressure and sound in essential time synchronism.
  • the output signals resulting from coincidence of the pressure and acoustic signals are then utilized to display or record automatically a pressure reading at points in time corresponding to the start and termination of the output signals.
  • FIG. 1 is a block diagram of the automatic blood pressure measuring system of this invention wherein the blood pressure is being taken from a patients arm;
  • FIG. 2 illustrates a pressure analog signal plot and pulse diagrams indicating conditions at correspondingly lettered points in the block diagram of FIG. 1, useful in explaining the operation of the system.
  • FIG. 1 there is shown a patient together with means for applying pressure to a portion of his body, such as his left arm 11, as by means of a flexible fluid chamber 12.
  • the chamber 12 may constitute a wrap-around flat tubular arrangement which can be secured so that increasing the fluid pressure within the chamber applies pressure to the arm 11.
  • an inlet tube 13 including an inlet control valve 14 in turn receiving fluid under pressure from a source 15.
  • the valve 14 is of the proportional type so that the rate of pressure build up or application to the fluid chamber 12 can be controlled by the degree of opening of the valve 14.
  • Means for gradually decreasing the pressure in the fluid chamber 12 includes an outlet tube 16 having an outlet valve 17.
  • the outlet valve 17 is also of the proportional type so that the rate of bleeding off of fluid pressure from the chamber can be controlled.
  • a pressure transducer 18 in the tube 13 serves to convert the actual pressure changes occurring in the fluid chamber 12 to an electrical analog signal.
  • a means for generating pressure pulses corresponding to the patients heartbeat takes the form of a differentiating circuit 19 connected to receive the analog signal from the pressure transducer 18.
  • the differentiating circuit 19 detects pressure fluctuations in the analog signal to provide essentially a series of electrical pressure pulses which are then passed through a filter and threshold detector network 20 to provide quantized electrical pressure signals. As shown, these electrical pressure signals are passed into one side of a coincidence circuit 21.
  • Means responsive to pulses in the downstream side of the close-off pressure point in the patients arm 11 are provided to generate acoustic pulses.
  • This means in the embodiment illustrated takes the form of an acoustical conduit22 with one end 23 in physical contact with the patients arm and its other end terminating in a microphone 24, preferably mounted in sound insulation and vibration isolating material 25 to shield the microphone from ambient noise and perturbations.
  • Acoustic pulses from the microphone are passed through a filter and threshold detector network 26 to provide quantized output electrical acoustic signals which are then passed through the other side of the coincidence circuit 21.
  • the coincidence circuit 21 will provide an output signal only when signals simultaneously occur at its first and second inputs. These output signals are passed to a measuring means 27 which may include a digital display and/or recording means.
  • the analog pressure signal is also passed to an analog-to-digital converter 28 which essentially converts the pressure values into digi tal coded signals.
  • analog-to-digital converter 28 which essentially converts the pressure values into digi tal coded signals.
  • coded signals are passed along a first line 29 into the measuring means 27, the measuring means being triggered to display or record the specific pressure coded signal fed thereto at the start of output signals received therein and at the termination of such output signals.
  • the coded signals are stored and updated during each output signal. After termination of the output signal the first and last stored coded signals are displayed.
  • the same coded signals are also passed along a line 30 to a logic control circuit 31 connected to control the action of the inlet and outlet valves 14 and 17 through summing junctions as shown. It will also be noted that the output signals from the coincidence circuit 21 are also passed to the logic control circuit 31 by way of line 32 and that differentiated signals from circuit 19 are passed to the summing junctions. The proportional operation of the valves 14 and 17 are thus responsive to pressure rates of change feedback signals from the differentiating circuit 19.
  • the respective steps or dwell periods might, for example, be one second in duration.
  • the inlet valve 14 of FIG. 1 is automatically closed and the outlet valve 17 opened very slightly to permit a gradual decrease in the pressure as indicated by the curve 33.
  • the overall analog pressure signal 33 there are slight pressure fluctuations in the overall analog pressure signal 33. These fluctuations, corresponding to the heartbeats of the patient, are accentuated in the range between the systolic and diastolic pressures.
  • Diagram C shows the pressure pulses after they have passed through the filter and threshold network 20 wherein it will be noted that they are essentially quantized to provide sharp individual pressure signals 36 of uniform amplitude.
  • Pulse diagram D inFIG. 2 illustrates the detected acoustic pulses some of which are shown at 37 from the microphone 24 of FIG. 1 which pulses are passed into the filter and threshold network 26. It will be noted that various extraneous noise signals and variations accompany the acoustic pulses and it is in the proper detection of the acoustic pulses resulting from a resumption of blood flow that is most important in providing accurate blood pressure measurements. As mentioned, the spurious signals which appear between the pulses have not been properly discriminated against in automatic apparatus heretofore proposed for making blood pressure measurements.
  • Diagram E shows the result of filtering and quantizing the acoustic pulses to provide uniform acoustic signals as at 38.
  • Pulse diagram F in FIG. 2 illustrates some of the output signals at 39 from the coincidence circuit 21. These output signals only occur upon time coincidence of the pressure signals 36 and the acoustic signals 38 and because of this correlation, it will be immediately evident that a substantial proportion of the extraneous unwanted signals are eliminated.
  • the fluid chamber 12 is initially applied to a portion of the patients body such as his 5 arm. Further, the small cup 23 at the end of the acoustical conduit 22 may be attached to the chamber so that it is secured to the lower portion of the patients upper arm in a position to detect acoustic pulses therein as a consequence of constricted blood flow.
  • the logic control circuit 31 for the inlet and outlet valves 14 and 17 is programmed and controlled by the fedback signals on the lines 30 and 32 and the differentiated signals from the circuit 19. Thus, upon starting a cycle of the equipment, the logic control 31 will open the inlet valve 14 to apply pressure fairly rapidly from the pressure source 15 to the fluid chamber 12.
  • the build up of pressure in the fluid chamber is shown by the analog pressure curve 33 wherein the build up rate is indicated at fifty millimeters per second.
  • the programmed pressure control in the logic circuit 31 is such as to cause the valve 14 to close when 120 millimeters of mercury pressure is reached, so that the pressure is held for a dwell period of, for example, one second as indicated At the second dwell period, it will be noted that the pressure is above the represented systolic pressure and therefore flow has been blocked off and there will be no acoustic pulses corresponding to 41 in diagram D detected. Thus the output signals 42 will terminate.
  • the pressure program in the logic control 31 is such as to effect one further pressure increase as a safety measure to make sure that blood flow is completely blocked. Thus, the pressure will increase in steps until two successive dwell periods have passed at which no acoustic pulses such as indicated at 41 are detected.
  • this pressure is 160 millimeters of mercury but in the event that pressure pulses were detected during the dwell period at one-forty or one-sixty, the build up would continue as indicated by the dotted lines.
  • the inletvalve 14 is closed and the outlet valve 17 of FIG. 1 is opened slightly to permit a gradual decrease in pressure. This decrease may be at the rate, for example, of 2 millimeters per second.
  • the gradually decreasing pressure will continue until a point is reached at which blood flow will start to the lower extremity of the arm.
  • this pressure corresponds to the systolic blood pressure and in the example of FIG. 2 occurs at about 138 millimeters of mercury.
  • the resumption of flow is marked by accentuation of pressure pulses as indicated at 33' giving rise to pressure signals as shown at 36'.
  • Resumption of-flow is also marked by the detection of the acoustic pulses 37 as shown in diagram D. An output electrical signal from the coincidence circuit will only occur when the acoustic pulses are in time synchronism with the pressure pulses 35 as correlated by coincidence of the pressure and acoustic signals 36 and 38.
  • the start of the output signals 39 triggers the measuring means 27 in FIG. 1 to record the systolic pressure as provided by the coded signals on line 29. This pressure could as well be visually displayed.
  • Termination of the output pulses 39 as will occur when the diastolic pressure is reached also triggers the measuring means 27 to record and/or display the corresponding diastolic pressure as provided by the coded signals and stored during the last output pulse.
  • the essence of the present invention resides in providing at least two independent signals corresponding, first, to the patients heartbeat in the form of pressure signals, and second, to acoustic signals caused by constricted blood flow in the downstream portion of the circulatory system which is closed off. Time correlation of these signals then provides accurate output signals which are relatively clear of extraneous pressure pulses or spurious signals. The start and termination of the generated output signals are then utilized to trigger the proper display of the systolic and diastolic pressures or as mentioned automatically record such pressures.
  • a method of automatically measuring a patients systolic and diastolic blood pressure comprising the steps of:
  • a system for automatically measuring the systolic and diastolic blood pressures of a patient comprising, in combination:
  • e. means responsive to pulses in the downstream side of the close-off pressure point in the patients circulatory system to detect acoustic pulses
  • filtering and threshold detecting means for respectively filtering and detecting said pressure and acoustic pulses and respectively providing quantized individually defined electrical pressure and acoustic signals
  • coincidence circuit means receiving said pressure and acoustic signals and providing an output signal only upon coincidence of a pressure signal and an acoustic signal
  • measuring means connected to receive the output signals and responsive to said analog pressure signal to provide indications of the pressure detected by said pressure transducer meansat the start and termination of said output signals, whereby the systolic and diastolic blood pressures are automatically measured.
  • said means for applying pressure includes a flexible fluid chamber arranged to surround said portion of the patient and having an inlet fluid line and associated inlet control valve, said means for gradually decreasing the applied pressure including an outlet fluid line from said chamber and associated outlet control valve, said means responsive to the patients heartbeat to detect pressure pulses including a differentiating circuit receiving said analog pressure signal and providing said pressure pulses in response to pressure fluctuations in said analog pressure signal; an analog-to-digital converter responsive to said analog pressure signal to generate digital coded signals indicative of the pressure, said coded signals being applied to and stored in said measuring means; and a logic control circuit connected to said inlet and outlet control valves and connected to receive said coded signals and said output signals whereby automatic proportional opening and closing of the valves is controlled by the coded and output signals in accord with a programmed application of pressure and gradual decreasing of pressure to be provided in said fluid chamber.
  • said means responsive to pulses downstream of the close-off pressure point includes an acoustical conduit with one end in physical contact with said portion of the patient and its other end terminating in a microphone for receiving sound in said conduit and converting the sound into said acoustic pulses, there being provided insulation material around said microphone to shield it from ambient noise and vibration.
  • measuring means includes means providing a visual digital display of the systolic and diastolic blood pressures.
  • measuring means includes means for automatically recording said systolic and diastolic blood pressures.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Cardiology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Public Health (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)
  • Vascular Medicine (AREA)
  • Veterinary Medicine (AREA)
  • Acoustics & Sound (AREA)
  • Physiology (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Hematology (AREA)
  • Ophthalmology & Optometry (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
US443442A 1974-02-19 1974-02-19 Blood pressure measuring system Expired - Lifetime US3905354A (en)

Priority Applications (6)

Application Number Priority Date Filing Date Title
US443442A US3905354A (en) 1974-02-19 1974-02-19 Blood pressure measuring system
CA219,946A CA1005563A (en) 1974-02-19 1975-02-12 Blood pressure measuring system
GB593475A GB1460413A (en) 1974-02-19 1975-02-12 Method of and apparautus for measuring blood pressure polyurethane elastomers
DE19752506651 DE2506651A1 (de) 1974-02-19 1975-02-17 Verfahren und einrichtung zur messung des systolischen und diastolischen blutdrucks
JP50019496A JPS50118588A (de) 1974-02-19 1975-02-18
FR7505046A FR2260975A1 (de) 1974-02-19 1975-02-18

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US (1) US3905354A (de)
JP (1) JPS50118588A (de)
CA (1) CA1005563A (de)
DE (1) DE2506651A1 (de)
FR (1) FR2260975A1 (de)
GB (1) GB1460413A (de)

Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4005701A (en) * 1975-06-11 1977-02-01 Whittaker Corporation Noise rejecting electronic sphygmomanometer and methods for measuring blood pressure
US4011860A (en) * 1975-10-20 1977-03-15 Filac Corporation Calibrated blood pressure measuring system and method
US4026277A (en) * 1974-04-12 1977-05-31 Matsushita Electric Industrial Co., Ltd. Blood pressure measuring apparatus
US4033336A (en) * 1975-11-19 1977-07-05 Medical Scientific International Corporation System for sensing and recording medical information
US4058117A (en) * 1975-10-17 1977-11-15 Palo Alto Research Associates Blood pressure measuring apparatus
US4177801A (en) * 1976-07-30 1979-12-11 Dubernard Hospital, S.A. Process and apparatus for the non-intrusive measurement of circulatory parameters
US4188955A (en) * 1977-09-12 1980-02-19 Omron Tateisi Electronics Co. Blood pressure measuring process and apparatus
US4214589A (en) * 1977-09-14 1980-07-29 Omron Tateisi Electronics Co. Method and apparatus for blood pressure measurement including a true Korotkov sound detector
EP0014720A1 (de) * 1977-11-15 1980-09-03 Matsushita Electric Works, Ltd. Sphygmomanometer
EP0020110A1 (de) * 1979-05-25 1980-12-10 William John Kaspari Unblutig wirkende Sonde für Blutdrucksignale
US4252127A (en) * 1979-06-19 1981-02-24 Iowa State University Research Foundation Portable blood pressure recorder
US4271843A (en) * 1978-10-10 1981-06-09 Flynn George J Method and apparatus for diastolic pressure measurement
US4294261A (en) * 1976-06-01 1981-10-13 The United States Of America As Represented By The United States National Aeronautics And Space Administration Logic-controlled occlusive cuff system
US4312359A (en) * 1980-02-19 1982-01-26 Life Care Systems, Inc. Noninvasive blood pressure measuring system
US4337778A (en) * 1979-08-01 1982-07-06 Omron Tateisi Electronics, Inc. Blood pressure measuring apparatus
US4367751A (en) * 1976-12-27 1983-01-11 Warner-Lambert Company Apparatus and process for producing artifact effect on sphygmometric information
WO1984000290A1 (en) * 1982-07-19 1984-02-02 Bomed Medical Mfg Non-invasive real time blood pressure measurement system
US4432373A (en) * 1980-02-19 1984-02-21 Omron Tateisi Electronics Company Electronic blood pressure measuring apparatus
US4459991A (en) * 1980-02-18 1984-07-17 Asulab A.G. Blood pressure measuring equipment
US4493326A (en) * 1979-10-03 1985-01-15 United States Surgical Corporation Automatic blood pressure system with servo controlled inflation and deflation
US4567899A (en) * 1984-07-30 1986-02-04 Healthcheck Corporation Cuff pressure controller for blood pressure measurement apparatus
US4646749A (en) * 1983-08-03 1987-03-03 Henri Berger Apparatus and a process for measuring the blood pressure by an indirect method
US4729382A (en) * 1986-09-02 1988-03-08 Schaffer John D Method and apparatus for automatically determining pulse rate and diastolic and systolic blood pressure
EP0337161A1 (de) * 1988-03-24 1989-10-18 Spacelabs, Inc. Blutdruckmanschette mit integraler Tonfühlerschale
US5054495A (en) * 1989-07-10 1991-10-08 Colin Electronics Co., Ltd. Automatic blood-pressure measuring apparatus
US20060036185A1 (en) * 2004-08-14 2006-02-16 Lewicke John A Patient monitoring system with blood pressure measurement capacity
US20070032729A1 (en) * 2003-10-21 2007-02-08 Juergen Fortin Device and method for controlling the pressure in an inflatable cuff of a blood pressure manometer
CN106725401A (zh) * 2017-01-12 2017-05-31 成都信息工程大学 基于深度学习的自动血压测量方法
US20210022627A1 (en) * 2017-09-14 2021-01-28 Koninklijke Philips N.V. Inflation apparatus for an inflation-based non-invasive blood pressure monitor and a method of operating the same

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4313445A (en) * 1977-10-25 1982-02-02 Ivac Corporation Electronic sphygmomanometer
JPS5482889A (en) * 1977-12-14 1979-07-02 Fujitsu Ltd Automatic blood pressure measuring system
HU176288B (en) * 1977-12-21 1981-01-28 Medicor Muevek Apparatos to determine blood-pressure, in the first place, of babies not in a invasive way
US4328810A (en) * 1979-10-03 1982-05-11 United States Surgical Corporation Automatic blood pressure system
JPS596654B2 (ja) * 1980-08-25 1984-02-14 松下電工株式会社 電子式血圧計
US4660567A (en) * 1984-09-27 1987-04-28 Takeda Medical Company Limited Method of automatically measuring blood pressure, and apparatus therefor
FR2582122B3 (fr) * 1985-05-17 1987-08-21 Wegmann Raymond Dispositif de mesure automatique de la pression arterielle par monitorage autonome, informatise en ambulatoire vrai

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3126886A (en) * 1964-03-31 Automatic sphygmomanometer
US3508537A (en) * 1965-04-20 1970-04-28 Beckman Instruments Inc Method and apparatus for automatic blood pressure monitoring
US3533401A (en) * 1966-07-29 1970-10-13 Hellige & Co Gmbh F Apparatus for automatically measuring blood pressure
US3552381A (en) * 1967-05-23 1971-01-05 Bell Telephone Labor Inc Sphygmomanometric method and apparatus
US3654915A (en) * 1969-12-19 1972-04-11 Del Mar Eng Lab Apparatus for automatically measuring and indicating blood pressure
US3779235A (en) * 1971-06-18 1973-12-18 Searle Medidata Inc Cardiovascular test station pressurometer interface system
US3814083A (en) * 1972-05-24 1974-06-04 Nasa Apparatus and method for processing korotkov sounds

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3126886A (en) * 1964-03-31 Automatic sphygmomanometer
US3508537A (en) * 1965-04-20 1970-04-28 Beckman Instruments Inc Method and apparatus for automatic blood pressure monitoring
US3533401A (en) * 1966-07-29 1970-10-13 Hellige & Co Gmbh F Apparatus for automatically measuring blood pressure
US3552381A (en) * 1967-05-23 1971-01-05 Bell Telephone Labor Inc Sphygmomanometric method and apparatus
US3654915A (en) * 1969-12-19 1972-04-11 Del Mar Eng Lab Apparatus for automatically measuring and indicating blood pressure
US3779235A (en) * 1971-06-18 1973-12-18 Searle Medidata Inc Cardiovascular test station pressurometer interface system
US3814083A (en) * 1972-05-24 1974-06-04 Nasa Apparatus and method for processing korotkov sounds

Cited By (36)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4026277A (en) * 1974-04-12 1977-05-31 Matsushita Electric Industrial Co., Ltd. Blood pressure measuring apparatus
US4005701A (en) * 1975-06-11 1977-02-01 Whittaker Corporation Noise rejecting electronic sphygmomanometer and methods for measuring blood pressure
US4058117A (en) * 1975-10-17 1977-11-15 Palo Alto Research Associates Blood pressure measuring apparatus
US4011860A (en) * 1975-10-20 1977-03-15 Filac Corporation Calibrated blood pressure measuring system and method
US4033336A (en) * 1975-11-19 1977-07-05 Medical Scientific International Corporation System for sensing and recording medical information
US4294261A (en) * 1976-06-01 1981-10-13 The United States Of America As Represented By The United States National Aeronautics And Space Administration Logic-controlled occlusive cuff system
US4177801A (en) * 1976-07-30 1979-12-11 Dubernard Hospital, S.A. Process and apparatus for the non-intrusive measurement of circulatory parameters
US4367751A (en) * 1976-12-27 1983-01-11 Warner-Lambert Company Apparatus and process for producing artifact effect on sphygmometric information
US4188955A (en) * 1977-09-12 1980-02-19 Omron Tateisi Electronics Co. Blood pressure measuring process and apparatus
US4214589A (en) * 1977-09-14 1980-07-29 Omron Tateisi Electronics Co. Method and apparatus for blood pressure measurement including a true Korotkov sound detector
EP0014720A4 (de) * 1977-11-15 1980-09-29 Matsushita Electric Works Ltd Sphygmomanometer.
US4326536A (en) * 1977-11-15 1982-04-27 Matsushita Electric Works, Ltd. Sphygmomanometer
DE2857174C1 (de) * 1977-11-15 1982-09-02 Matsushita Electric Works, Ltd., Kadoma, Osaka Blutdruckmesser
EP0014720A1 (de) * 1977-11-15 1980-09-03 Matsushita Electric Works, Ltd. Sphygmomanometer
US4271843A (en) * 1978-10-10 1981-06-09 Flynn George J Method and apparatus for diastolic pressure measurement
EP0020110A1 (de) * 1979-05-25 1980-12-10 William John Kaspari Unblutig wirkende Sonde für Blutdrucksignale
US4252127A (en) * 1979-06-19 1981-02-24 Iowa State University Research Foundation Portable blood pressure recorder
US4337778A (en) * 1979-08-01 1982-07-06 Omron Tateisi Electronics, Inc. Blood pressure measuring apparatus
US4493326A (en) * 1979-10-03 1985-01-15 United States Surgical Corporation Automatic blood pressure system with servo controlled inflation and deflation
US4459991A (en) * 1980-02-18 1984-07-17 Asulab A.G. Blood pressure measuring equipment
US4312359A (en) * 1980-02-19 1982-01-26 Life Care Systems, Inc. Noninvasive blood pressure measuring system
US4432373A (en) * 1980-02-19 1984-02-21 Omron Tateisi Electronics Company Electronic blood pressure measuring apparatus
WO1984000290A1 (en) * 1982-07-19 1984-02-02 Bomed Medical Mfg Non-invasive real time blood pressure measurement system
US4646749A (en) * 1983-08-03 1987-03-03 Henri Berger Apparatus and a process for measuring the blood pressure by an indirect method
US4567899A (en) * 1984-07-30 1986-02-04 Healthcheck Corporation Cuff pressure controller for blood pressure measurement apparatus
US4729382A (en) * 1986-09-02 1988-03-08 Schaffer John D Method and apparatus for automatically determining pulse rate and diastolic and systolic blood pressure
EP0337161A1 (de) * 1988-03-24 1989-10-18 Spacelabs, Inc. Blutdruckmanschette mit integraler Tonfühlerschale
US4890625A (en) * 1988-03-24 1990-01-02 Spacelabs, Inc. Blood pressure cuff with integral acoustic pickup cup
US5054495A (en) * 1989-07-10 1991-10-08 Colin Electronics Co., Ltd. Automatic blood-pressure measuring apparatus
US20070032729A1 (en) * 2003-10-21 2007-02-08 Juergen Fortin Device and method for controlling the pressure in an inflatable cuff of a blood pressure manometer
US8114025B2 (en) * 2003-10-21 2012-02-14 Cnsystems Medizintechnik Gmbh Device and method for controlling the pressure in an inflatable cuff of a blood pressure manometer
US20060036185A1 (en) * 2004-08-14 2006-02-16 Lewicke John A Patient monitoring system with blood pressure measurement capacity
US7438687B2 (en) * 2004-08-14 2008-10-21 Nova Technology Corporation Patient monitoring system with blood pressure measurement capacity
CN106725401A (zh) * 2017-01-12 2017-05-31 成都信息工程大学 基于深度学习的自动血压测量方法
CN106725401B (zh) * 2017-01-12 2020-01-17 成都信息工程大学 基于深度学习的听诊器音频数据处理方法
US20210022627A1 (en) * 2017-09-14 2021-01-28 Koninklijke Philips N.V. Inflation apparatus for an inflation-based non-invasive blood pressure monitor and a method of operating the same

Also Published As

Publication number Publication date
GB1460413A (en) 1977-01-06
FR2260975A1 (de) 1975-09-12
DE2506651A1 (de) 1975-08-21
CA1005563A (en) 1977-02-15
JPS50118588A (de) 1975-09-17

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