EP2323545A2 - Capteur piezo-électrique de mesure de fluctuations de pression - Google Patents

Capteur piezo-électrique de mesure de fluctuations de pression

Info

Publication number
EP2323545A2
EP2323545A2 EP09749661A EP09749661A EP2323545A2 EP 2323545 A2 EP2323545 A2 EP 2323545A2 EP 09749661 A EP09749661 A EP 09749661A EP 09749661 A EP09749661 A EP 09749661A EP 2323545 A2 EP2323545 A2 EP 2323545A2
Authority
EP
European Patent Office
Prior art keywords
sensor
piezoelectric
pressure
measurement
blood pressure
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP09749661A
Other languages
German (de)
English (en)
Inventor
Roland Kopetsch
Mohammad Nasseri
Stephan Bergmann
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sectorcon Ingenieurgesellschaft fur System- und Softwaretechnik Mbh
Original Assignee
Sectorcon Ingenieurgesellschaft fur System- und Softwaretechnik Mbh
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 Sectorcon Ingenieurgesellschaft fur System- und Softwaretechnik Mbh filed Critical Sectorcon Ingenieurgesellschaft fur System- und Softwaretechnik Mbh
Publication of EP2323545A2 publication Critical patent/EP2323545A2/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—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
    • 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
    • A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
    • A61B5/02125—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics of pulse wave propagation time
    • 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
    • A61B5/026—Measuring blood flow
    • A61B5/0285—Measuring or recording phase velocity of blood waves
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
    • G01L9/00—Measuring steady of quasi-steady pressure of fluid or fluent solid material by electric or magnetic pressure-sensitive elements; Transmitting or indicating the displacement of mechanical pressure-sensitive elements, used to measure the steady or quasi-steady pressure of a fluid or fluent solid material, by electric or magnetic means
    • G01L9/0041—Transmitting or indicating the displacement of flexible diaphragms
    • G01L9/008—Transmitting or indicating the displacement of flexible diaphragms using piezoelectric devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0247—Pressure sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/04—Arrangements of multiple sensors of the same type
    • A61B2562/043—Arrangements of multiple sensors of the same type in a linear array
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—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
    • A61B5/02028—Determining haemodynamic parameters not otherwise provided for, e.g. cardiac contractility or left ventricular ejection fraction
    • A61B5/02035—Determining blood viscosity
    • 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
    • A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
    • A61B5/02116—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics of pulse wave amplitude
    • 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
    • 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
    • A61B5/02—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
    • A61B5/026—Measuring blood flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/03—Detecting, measuring or recording fluid pressure within the body other than blood pressure, e.g. cerebral pressure; Measuring pressure in body tissues or organs

Definitions

  • the invention relates to a piezoelectric sensor for the improved measurement of mechanical quantities such as force, pressure or measured variables derived therefrom, in particular a piezoelectric sensor with improved measurement signal sensitivity and temperature stability for measurements of temporally and spatially variable pressures and for a and two-dimensional determination of the position and rate of propagation of pressure fluctuations and pressure waves.
  • a preferred field of application of the invention is the non-invasive, low-load and continuous measurement of the pulse rate and the blood pressure in humans and animals by measuring the arterial pulse waves by means of a sensor equipped with piezoelectric PVDF films.
  • the directed deformation of a piezoelectric material in the direction of the polarization forms microscopic dipoles by shifting the negative and positive charge centers within the unit cells.
  • the summation over all unit cells of the crystal leads to a macroscopically measurable electrical voltage, which is directly proportional to the deformation in a defined deformation range during longitudinal deformation in the polarity direction.
  • Piezoelectric films today usually consist of polyvinylidene fluoride (PVDF short), a transparent, semi-crystalline fluorine thermoplastic, which is polarized to produce the piezoelectric properties, ie heated, one-dimensionally stretched and thereby exposed to the alignment of the dipoles a strong directional electromagnetic field. The resulting piezoelectric properties are therefore strongly dependent on the direction due to the monoaxial orientation.
  • PVDF foil is metallically coated in order to dissipate the resulting dipole charges during deformation. This metal coating usually consists of gold or copper-nickel alloys deposited on the foil.
  • the charges can then be tapped by means of electrodes on the edge of the piezoelectric film and converted by means of a charge amplifier (charge-voltage converter) into a measurable electrical voltage.
  • the human heart conveys, as a discontinuous positive displacement pump in its contraction phase, the blood through the arteries in the direction of the peripheral blood vessels, from where it returns to the heart via the venous blood vessel system.
  • the peak blood pressure in the aorta during the contraction phase of the heart is the systolic blood pressure, which essentially depends on the cardiac function parameters - the blood pressure in the aorta at the exit of the heart during its defluxation phase is the diastolic blood pressure, which is essentially the stroke volume and elasticity the aorta depends.
  • a cuff usually applied around the upper arm of a patient is initially inflated with an air pressure that is above the expected systolic blood pressure and causes the artery in the arm of the patient to be pushed far enough that the blood flow at this point in the artery is interrupted is.
  • the air pressure in the cuff is now slowly lowered by opening a valve.
  • the cuff pressure drops below the systolic pressure, blood flow in the blood vessel is restored in the contraction phase of the heart for the period in which the arterial pressure is higher than the cuff pressure.
  • the degree of turbulence increases, so that for example by means of a stethoscope during this period in the blood flow direction shortly behind the vessel constriction an increased flow noise or a noise through the vessel wall movement in rhythm with the heart rate, the so-called Korotkoff sound can be heard.
  • the systolic blood pressure in this procedure therefore results from the cuff pressure to be read, during which the Korotkoff noise is heard for the first time during the slow lowering of the cuff pressure.
  • the diastolic blood pressure results from the reading of the Cuff pressure, in which the Korotkoff sound is no longer heard for the first time with continued reduction in cuff pressure, since below the diastolic blood pressure no blood vessel constriction takes place. Also possible is the reverse order of the measurement steps by slow cuff pressure increase - from below up. It should be noted that in certain hypertensive patients, an auscultatory gap arises, ie the Korottkoffge Hursch disappears when lowering the pressure between the systolic and diastolic pressure. If the pressure is lowered further, the sound will recur and the diastolic pressure will be determined when the Korottkoff sound disappears again.
  • Such a method for noninvasive measurement of blood pressure is described in DE 3424536, in which an inflatable arm cuff contains a microphone for receiving the Korotkoff noises and the systolic and diastolic blood pressure is determined and displayed by means of a digital evaluation unit.
  • the measurement accuracy of this method is not very high, especially for the determination of the diastolic blood pressure, and it is not suitable for continuous monitoring of the blood pressure, since the slow cuff pressure change makes each measuring process take a long time and a more frequent repetition of the measurements than every 5 minutes leads to a measurement falsification leads.
  • the patient is stressed by the high cuff pressure and there is a risk of tissue damage at the application site.
  • blood pressure is measured non-invasively and continuously without the use of troublesome and cumbersome compression cuffs.
  • the systolic blood pressure correlates quite well with the propagation velocity of a pulse wave or the reciprocal of the pulse transit time in the artery of a human.
  • P.Eiter analytically proves this connection by using an undamped wave and a lossless flow as a hydraulic replacement model for the pulse wave propagation in an artery in an elastic tube, neglecting external forces such as gravity presupposes and the relationship
  • p (2p / E p ) (R / h) c 2 -Eo / Ep (1)
  • p is the blood pressure in the artery
  • p is the blood density
  • R is the internal radius of the artery
  • h is the arterial wall thickness
  • c is the pulse wave velocity
  • E 0 and E p are empirical elastic constants used to describe arterial wall elasticity.
  • P.Eiter conducts the statistical proof of the correlation of the systolic blood pressure with the propagation velocity of a pulse wave or the reciprocal value of the pulse transit time in his thesis.
  • DE 10214220 accordingly describes a method and a device for the non-invasive, low-stress and continuous measurement of the pulse and the blood pressure by determining the pulse wave velocity.
  • the measurement of the systolic blood pressure which is usually particularly stressful for the patient, takes place by determining the pulse transit time by means of at least two pressure sensors, preferably on the upper and lower arm, in particular on the basis of piezoelectric foils.
  • the determined pulse transit times or systolic blood pressure values are stored in an evaluation unit.
  • the measurement of the diastolic blood pressure is carried out in particular by the oscillometric method by means of an arm sleeve, which is acted upon only with a pressure in the order of magnitude of the diastolic blood pressure, whereby the burden of the patient and the body tissue at the application site even with a long-term monitoring of blood pressure is low.
  • the two calibration measurements for systolic blood pressure determination by means of pulse transit time measurement are performed here oscillometrically by means of the arm sleeve at the beginning of the measurement interval.
  • the disadvantages here are that at least two pressure sensors at two measuring locations are necessary for determining the pulse transit time and that the measuring sensitivity is too low in the case of the pressure sensors based on piezoelectric films available in the prior art, in particular in patients with blood circulation. Disorders of the extremities, for example, in patients who have diabetes or the so-called smoker's leg.
  • the permanent application of a pressure cuff for the measurement according to a Riva-Rocci method is also necessary here.
  • the bias is thus neither on train nor in the direction of the piezo-dipole orientation, so that the force sensor presented here experiences no improvement in measurement sensitivity in the piezo-dipole direction due to the elastic bias due to the reduced influence of the signals by the other active components.
  • EP 370 203 describes an acceleration sensor in which a piezo film element is clamped over a defined preformed bottom of a metallic carrier part, the bottom serving to cause the piezo film to hit the ground with a correspondingly high acceleration and thus to cause excessive stretching of the piezoelectric film Piezo foil prevented.
  • the piezo film is thus not defined in piezo-dipole orientation biased to train and the cavity between the piezo film and the support member is not the fitting of the piezoelectric foil, for. for pressure wave detection on an uneven surface.
  • a pressure sensor based on piezoelectric transducers in particular piezoelectric foils, with the aid of which it is possible to measure temporally and / or spatially variable pressures as well as measurable quantities derived therefrom with improved measuring sensitivity.
  • a further object of the present invention is to provide a pressure sensor based on piezoelectric transducers, in particular piezoelectric foils, with the aid of which it is possible to measure temporally and / or spatially variable pressures as well as measured variables derivable therefrom with improved temperature stability of the measured data.
  • a further object of the present invention is to provide a pressure sensor based on piezoelectric transducers, in particular piezoelectric foils, which is kind to the skin.
  • a further object of the present invention is to provide a pressure sensor based on piezoelectric transducers, in particular piezoelectric foils, with the aid of which the determination of the position and propagation velocity of pressure fluctuations and pressure waves as well as measurement variables derivable therefrom can be performed with only one measuring sensor Only one location is possible.
  • a further object of the present invention is to provide a pressure sensor based on piezoelectric transducers, in particular piezoelectric foils, with the aid of which the measurement of temporally and / or spatially variable pressures as well as measurable variables can also be applied to irregularly shaped surfaces such as the human skin with improved sensitivity is enabled.
  • a further object of the present invention is to provide a pressure sensor based on piezoelectric transducers, in particular piezoelectric foils, with the aid of which the non-invasive, stress-free and continuous measurement and monitoring of the pulse rate as well as the systolic and diastolic blood pressure in humans and animals without continuous application a pressurized cuff for measurement according to a Riva-Rocci method is made possible.
  • the main characteristic of the invention is that in the pressure sensor according to the invention, a plurality of parallel strips of a piezoelectric material as a measuring membrane such a sensor base body is assigned such that they are biased one-dimensional elastic in the direction of the piezo-dipole orientation to train and between the spanned piezoelectric sensor material in Measuring range and the sensor base body by recess / cutout a free cavity is present.
  • the strong directionality of piezoelectric materials is used by their monoaxial orientation targeted to improve the measurement sensitivity.
  • a further improvement of the sensor measurement sensitivity is achieved by the plurality of parallel piezoelectric sensor material strips, since in the data evaluation by the sensor controller only the measurement signals of the piezoelectric sensor material strips are selected for data processing whose measurement signals are best.
  • the temperature stability of the measured data is improved by reduced heat flow of the sensor material to the sensor base body and the sensor material in the measuring range can be on irregularly shaped measuring surfaces such as the skin of the Clinging people optimally, whereby the sensor sensitivity is further improved.
  • the distance between the parallel piezoelectric sensor material strips to each other is known, with only one measuring sensor position and speed of propagation of pressure fluctuations and pressure waves and derived therefrom measurable variables perpendicular to the sensor material strips as the pulse wave velocity in animals and humans, or . By calibration measurement at a different angle, the measurement accuracy is highest with vertical arrangement of the sensor material strips to the pressure fluctuation propagation direction.
  • the blood pressure and the pulse rate in emergency patients with very low blood pressure and in patients with circulatory disorders of the extremities, ie, for example, in patients who have diabetes or the so-called smoker's leg are measured.
  • Another advantage of the invention is that the positioning of the sensor is simplified by the plurality of piezosensor strips on a sensor, since it does not have to be positioned as precisely on the site of the pressure fluctuation as, for example, an artery due to the measurement signal redundancy.
  • piezoelectric films in particular metallically coated polyvinylidene fluoride films (PVDF films for short), are used as piezoelectric transducers of the pressure sensors.
  • PVDF films metallically coated polyvinylidene fluoride films
  • the PVDF film of the pressure sensor is coated on its metallic side with a protective film and bonded as a measuring membrane laminate on a flexible printed circuit board, preferably made of polyimide.
  • the sensor base body on which the measuring membrane laminate is adhered under tension designed as a rigid, rigid carrier board on which the amplifier electronics of the piezoelectric transducer is soldered directly.
  • two superimposed measuring membrane laminate layers whose sensor material strip orientation is preferably perpendicular to one another are used to provide a two-dimensional determination of the position and the propagation velocity of pressure fluctuations and pressure waves as well as measurement variables derivable therefrom, such as the arterial pulse wave velocity Animal and human at any rotational arrangement of the sensor to allow on the site.
  • juxtaposed regions of measuring membrane laminates whose sensor material strip orientation is preferably perpendicular to one another are used to determine the position and the propagation velocity of pressure fluctuations and pressure waves as well as parameters derived therefrom, such as the arterial pulse wave velocity to allow for animal and human at any rotational arrangement of the sensor at the site.
  • FIG. 1 shows a piezoelectric sensor according to the invention in cross section
  • FIG. 2 shows a piezoelectric sensor according to the invention in a bottom view
  • FIG. 3 shows a measuring and evaluation device according to the invention applied to the arm of a patient in a perspective view.
  • a sensor base body 4 which is designed as a rigid carrier board to which the amplifier electronics 6 (charge amplifier) is soldered directly to avoid charge losses.
  • the measuring membrane laminate which consists of a flexible polyimide circuit board 3, a plurality parallel metallic coated PVDF film strip 1 and a polyimide protective film 2, glued in such a way that between the measuring membrane laminate and the sensor base 4, a cavity 5 is formed, for example, by milling the sensor base body support plate 4 made can be, and that the measuring membrane laminate is biased in the direction of piezopolarization of the PVDF film strip 1 to train.
  • Amplifier electronics 6, sensor base support plate 4, the polyimide circuit board 3 and the metallic side of the PVDF film strips 1 are electrically conductively connected by means of electrodes and printed circuit board not shown here.
  • the protective film 2 protects the PVDF film strips from moisture and dirt and thus protects against oxidation of the metallic electrodes. In addition, a good skin compatibility is achieved.
  • the resulting cavity 5 facilitates the fitting of the measuring membrane laminate on uneven surfaces such as the human skin and thus improves the measured data quality.
  • the cavity 5 also reduces and calculates the heat flow between the PVDF film strip 1 and the sensor main body support board 4, so that the temperature stability of the measurement data is improved.
  • FIG. 2 illustrates, in the view from below, the four parallel PVDF film strips 1 glued onto the sensor base body 4 in a tension-biased manner to form a cavity 5 by milling out the rigid carrier board as the sensor base 4 on it as a measuring membrane Laminate are glued.
  • FIG. 3 shows as an exemplary embodiment of a piezoelectric sensor for pressure fluctuation measurement according to the invention the structure of a device for non-invasive, low-stress and continuous measurement and monitoring of the blood pressure and the pulse rate in humans.
  • a Velcro 18 arm sleeve 7 is applied, which has at least one pressure pad 8, for example, is filled with a measuring liquid to calibrate the measurement of diastolic and systolic blood pressure.
  • the pressure pad 8 is designed on the skin-facing side as an elastic membrane.
  • the arm sleeve 7 also contains a piezoelectric pressure sensor according to the invention as a pulse wave sensor 12, which can be applied by appropriate attachment of the sleeve 7, for example on the arm of the patient 16 in the artery and consists of several parallel PVDF piezo film strips 1, which on a rigid carrier board with directly integrated amplifier electronics 6 are glued as a sensor base body 4 to form a cavity 5 between PVDF piezo film 1 and sensor base body 4 biased to train.
  • the PVDF piezo film strips 1 are bonded as a measuring membrane laminate with a polyimide protective film and a flexible polyimide printed circuit board.
  • an electrical voltage signal is generated in the PVDF film strip 1 of the pulse wave sensor 12 by stretching the piezoelectric material, which is amplified in the amplifier electronics 6 and evaluated in the control and evaluation unit 13.
  • the systolic and diastolic blood pressure is determined in the control and evaluation unit 13.
  • the display of the measured values and the menu navigation takes place by means of an LCD film 14, the input for device control by means of a keyboard 15.
  • a calibration routine is started by the control and evaluation unit 13.
  • the pressure in the pressure pad 8 is slowly increased by means of the pump 9 and determined by means of the oscillometric sensor 11 of the diastolic and systolic blood pressure of the patient.
  • the pulse transit times and the pulse wave signal shape are determined by at least two of the parallel PVDF foil strips 1, and by assigning the pulse transit time values and the pulse wave signal shape to the pressure values in the pressure pad 8 determined oscillometrically during systole and diastole. measured by means of the pressure sensor 10, the measuring device for the determination of the systolic and diastolic blood pressure calibrated.
  • the calibration procedure is carried out by at least two calibration measurements, for example when the patient is at rest and after a short movement phase of the patient to increase the blood pressure.
  • the threshold value of the systolic and diastolic blood pressure can be used to trigger a possible alarm function.
  • the pressurization of the pressure pad 8 is done automatically by an oscillometric sensor 11 detects the Pulsoszillationsamplituden and passes as an electrical signal to a control and evaluation unit 13, where it is decided by a threshold value of the Pulsoszillationsamplitude whether the pressure in the pressure pad corresponds to the diastolic or systolic blood pressure , If the threshold value is lower or higher, the control and evaluation unit 13 causes the pump 9 to adjust the pressure in the pressure pad 8.
  • the oscillometric sensor 11 may be on the elastic Membrane of the pressure pad 8 may be attached.
  • the pressure in the pressure pad 8 is recorded by a pressure sensor 10 and evaluated and stored in the control and evaluation unit 13 as diastolic or systolic blood pressure for calibrating the measuring arrangement.
  • the pulse transit time values and pulse wave signal shapes are now continuously transmitted to the control and evaluation unit 13 by means of the pulse wave sensor 12 without the patient burdening the arm sleeve 7, where the conversion to the systolic and diastolic blood pressure values takes place and these are stored ,
  • an adjustable threshold value of the diastolic and systolic blood pressure is exceeded, an alarm function can be triggered, which can either be part of the control and evaluation unit 13 or takes place via the data interface 17 by an external device.
  • This data interface 17 can be designed, for example, as a data cable plug connection, infrared or radio interface. By means of the data interface 17, these blood pressure data can also be transferred to external devices such as a PC and further evaluated.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Cardiology (AREA)
  • Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Surgery (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Veterinary Medicine (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Physiology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Vascular Medicine (AREA)
  • Hematology (AREA)
  • General Physics & Mathematics (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

La présente invention concerne un capteur piézo-électrique destiné à réaliser une mesure améliorée de grandeurs mécaniques telles qu'une force, une pression ou des grandeurs de mesure dérivées, en particulier un capteur mince PVDF ayant une sensibilité au signal de mesure et une stabilité à la température améliorées lors de mesures de pressions variables dans le temps et/ou dans l'espace, et pour la détermination monodimensionnelle ou bidimensionnelle de la position et de la vitesse de propagation de fluctuations de pression et d'ondes de pression au moyen d'un seul capteur de mesure en un emplacement de mesure. Un champ d'application préféré de l'invention est la mesure non invasive, peu contraignante et continue du pouls et de la pression sanguine systolique et diastolique chez des êtres humaines et des animaux par détermination de la vitesse des ondulations de pouls et de la forme du signal des ondulations de pouls, l'invention ayant pour objet de permettre, à l'aide d'un seul capteur en un emplacement de mesure, grâce à la sensibilité de mesure améliorée du capteur piézo-électrique, la mesure de la tension artérielle et du pouls par exemple chez des patients faisant l'objet d'une urgence et ayant une tension artérielle très faible et chez des patients présentant des problèmes de circulation sanguine des extrémités, par exemple chez des patients atteints de diabète ou souffrant de la "jambe du fumeur", en rendant inutile l'application à long terme d'un brassard sous pression pour la mesure et la surveillance continues de la tension artérielle. A cet effet, une pluralité de bandes parallèles en matériau piézo-électrique (1) disposées dans le capteur de pression de l'invention en tant que membrane de mesure, sont associées au corps de base (4) du capteur de sorte qu'elles sont précontraintes en traction de façon monodimensionnelle et élastique en direction de l'orientation piézo-électrique dipolaire, et un espace creux vide (5) est formé par évidement/fraisage entre le matériau piézo-électrique (1) sous tension du capteur dans la zone de mesure et le corps de base (4) du capteur.
EP09749661A 2008-05-20 2009-07-17 Capteur piezo-électrique de mesure de fluctuations de pression Withdrawn EP2323545A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102008024737A DE102008024737B3 (de) 2008-05-20 2008-05-20 Piezoelektrischer Sensor zur Druckfluktuationsmessung
PCT/EP2009/005543 WO2009141171A2 (fr) 2008-05-20 2009-07-17 Capteur piezo-électrique de mesure de fluctuations de pression

Publications (1)

Publication Number Publication Date
EP2323545A2 true EP2323545A2 (fr) 2011-05-25

Family

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US20120065526A9 (en) 2012-03-15
US9642539B2 (en) 2017-05-09
DE102008024737B3 (de) 2010-01-07
WO2009141171A3 (fr) 2010-08-19
WO2009141171A2 (fr) 2009-11-26
US20110166459A1 (en) 2011-07-07

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