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WO2015092753A1 - Procédé amélioré de surveillance de la pression artérielle - Google Patents

Procédé amélioré de surveillance de la pression artérielle Download PDF

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Publication number
WO2015092753A1
WO2015092753A1 PCT/IB2014/067110 IB2014067110W WO2015092753A1 WO 2015092753 A1 WO2015092753 A1 WO 2015092753A1 IB 2014067110 W IB2014067110 W IB 2014067110W WO 2015092753 A1 WO2015092753 A1 WO 2015092753A1
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WO
WIPO (PCT)
Prior art keywords
pressure
sensor
user
tissue
signal
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/IB2014/067110
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English (en)
Inventor
Joonas MAKKONEN
Ulf MERIHEINÄ
Pekka Kostiainen
Antti FINNE
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.)
Murata Manufacturing Co Ltd
Original Assignee
Murata Manufacturing Co 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
Priority claimed from FI20136306A external-priority patent/FI20136306L/fi
Application filed by Murata Manufacturing Co Ltd filed Critical Murata Manufacturing Co Ltd
Publication of WO2015092753A1 publication Critical patent/WO2015092753A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics

Definitions

  • the present invention relates to monitoring vital signs of a user and especially to a device, system, method and a computer program product for monitoring blood pressure information of a user according to the preambles of the independent claims.
  • HTN also called as High Blood Pressure, HBP
  • HBP High Blood Pressure
  • Patent publication US6,533,729 discloses a blood pressure sensor that includes a source of photo-radiation, an array of photo-detectors, and a reflective surface that is placed adjacent to the location where the blood pressure data is to be acquired. Blood pressure fluctuations translate to deflections of the patient's skin and these deflections show as scattering patterns detected by the photo-detectors.
  • the solution relieves users of cuffs and compressors, but it requires a relatively complicated calibration procedure using known blood pressure data and scattering patterns, which are obtained while the known blood pressure is obtained at a known hold down pressure. During data acquisition, scattering patterns are linearly scaled to the calibrated values of signal output and hold down pressure.
  • Patent application publication US2005/0228299 discloses a patch sensor for measuring blood pressure without a cuff. Also this solution requires a separate calibration process that applies a conventional blood pressure cuff to generate a calibration table to be used in subsequent measurements.
  • the object of the present invention is to provide an improved non-invasive blood pressure information monitoring solution where at least one of the disadvantages of the prior art are eliminated or at least alleviated.
  • the objects of the present invention are achieved with a device, system, method and a computer program product according to the characterizing portions of the independent claims.
  • the present invention is based on measuring and analysing a pulse wave for estimating diastolic and systolic blood pressure.
  • the configuration is unnoticeable; still it provides very accurate results.
  • a device comprising at least one sensor.
  • the device comprises a fastening element for detachably attaching the sensor to a position on the outer surface of a tissue of a user.
  • the sensor is configured to generate a signal that varies according to deformations of the tissue in response to an arterial pressure wave expanding or contracting a blood vessel underlying the tissue in the position.
  • a processing component is configured to input the signal and compute from the signal pulse wave parameters representing detected characteristics of the progressing arterial pressure wave of the user.
  • the processing component configured to compute from the pulse wave parameters blood pressure value of the user.
  • the sensor may be, for example, a pressure sensor or a photoplethysmograph.
  • a method comprising monitoring blood pressure information of a user with a device, comprising a sensor, and a fastening element.
  • the method comprises the steps of detachably attaching the sensor to a position on the outer surface of a tissue of a user, generating with the sensor a signal that varies according to deformations of the tissue in response to an arterial pressure wave expanding or contracting a blood vessel underlying the tissue in the position.
  • the method further comprises inputting by a processing component the signal and computing from the signal pulse wave parameters representing detected characteristics of the progressing arterial pressure wave of the user and computing by the processing component from the pulse wave parameters blood pressure value of the user.
  • the sensor may be, for example, a pressure sensor or a photoplethysmograph.
  • Figure 2a and 2b illustrates functional example configuration of a blood pressure information monitoring system
  • Figure 3a and 3b illustrate example arrangements of sensors in the device
  • Figure 4 illustrates an example pulse wave
  • Figure 5 illustrates an example flow chart of a measurement
  • Figure 5 illustrates an example chart of parameters and coefficients
  • Figure 6 illustrates example parameters and corresponding correlation coefficients for pulse wave parameters and person related parameters
  • Figure 7 illustrates an embodiment, where the signal is generated by means of a photoplethysmograph.
  • the monitoring system comprises a device that generates one or more output values that represent detected characteristics of arterial pressure waves of a user. These values may be used as such or be further processed to indicate blood pressure information of the user.
  • the block charts of Figure la and lb illustrates functional elements of embodiments of a device 100 according to examples of the present invention. In this example, one or more pressure sensors are used for generating the signal. It is noted that the Figure is schematic; some proportions of the elements may be exaggerated to demonstrate the functional concepts of the embodiment.
  • the device 100 comprises a first pressure sensor (SI) 102, an optional second pressure sensor (S2) 104, a fastening element 106, and a processing component (DSP) 108. It is noted that in some embodiments the device 100 may comprise more than two pressure sensors.
  • a pressure sensor refers here to a functional element that converts ambient pressure into mechanical displacement of a diaphragm, and translates the displacement into an electrical signal.
  • the device 100 comprises at least one pressure sensor. It is clear to a person skilled in the art that additional pressure sensors may be included to the device without deviating from the scope of protection. Any pressure sensor of the pressure sensors included in a device may be applied in the claimed manner. Advantageously capacitive high resolution pressure sensors are applied due to their low power consumption and excellent noise performance. Other types of pressure sensors, for example piezoresistive pressure sensors, may be applied, however, without deviating from the scope of protection.
  • the first pressure sensor 102 is detachably attached to a first position
  • the optional second pressure sensor 104 is detachably attached to a second position on the outer surface 110 of a tissue 112 of a user.
  • the first position and the second position are separated by a predefined sensor distance d.
  • the positions are selected such that the sensors are placed along a blood vessel 120 underneath the tissue of the user.
  • the positions may be, for example, in an arm of a user. Other positions on the body of the user may be applied as well within the scope of protection.
  • the tissue 112 may be for example skin of the user.
  • the at least one pressure sensor is attached to the tissue with a fastening element 106 such that when an arterial pressure wave of blood expands or contracts the blood vessel 120 underlying the tissue, the tissue deforms and the pressure between the tissue and the fastening element varies according to deformations of the tissue.
  • the fastening element 106 refers here to mechanical means that may be applied to position the pressure sensors 102, 104 into contact with the outer surface 110 of the tissue 112 of the user.
  • the fastening element 106 may be implemented, for example, with an elastic or adjustable strap.
  • the pressure sensors 102, 104 and any electrical wiring required by their electrical connections may be attached or integrated to one surface of at least part of the strap. Other mechanisms may be applied, and fastening element 106 may apply other means of attachment, as well.
  • fastening element 106 may comprise easily removable adhesive bands to attach the pressure sensors on the tissue.
  • the device also comprises a processing component 108 that is electrically connected to the first pressure sensor 102 and the second pressure sensor 104 for further processing input signals generated by the pressure sensors.
  • the processing component 108 illustrates here any configuration of processing elements included in the device 100.
  • Advanced microelectromechanical pressure sensors are typically packaged sensor devices that include a micromachined pressure sensor and a measuring circuit.
  • the device 100 may include a further processing element into which pre-processed signals from the pressure sensor are delivered through predefined sensor device interfaces.
  • the processing component 108 may be a combination of one or more computing devices for performing systematic execution of operations upon predefined data. Such processing component essentially comprises one or more arithmetic logic units, a number of special registers and control circuits.
  • the processing component 108 may comprise or may be connected to a memory unit that provides a data medium where computer-readable data or programs, or user data can be stored.
  • the memory unit may comprise volatile or non-volatile memory, for example EEPROM, ROM, PROM, RAM, DRAM, SRAM, firmware, programmable logic, etc.
  • Figures 2a and 2b illustrate a functional configuration of a blood pressure information monitoring system 200 that includes the device 100 of Figure 1.
  • the first pressure sensor 102 in the first position is exposed to pressure PI, and is configured to generate a first signal Poutl .
  • the first signal corresponds to a pressure between the fastening element 106 and the tissue 112 of the user, which pressure varies according to deformations of the tissue 112 when an arterial pressure wave expands or contracts a blood vessel 120 underneath the tissue 112 in the first position.
  • the optional second pressure sensor 104 is exposed to pressure P2, and is configured to generate a second signal Pout2.
  • the second signal corresponds to a pressure between the fastening element 106 and the tissue 112 of the user, which pressure varies according to deformations of the tissue in response to the arterial pressure wave expanding or contracting the blood vessel 120 underlying the tissue in the second position.
  • the first signal Poutl and the optional second signal Pout2 are input to the processing component 108 that is configured to use them to compute one or more output values Px, Py, Pz, each of which represents a detected characteristic of the arterial pressure wave of the user.
  • the detected characteristic may be, for example, a detected pressure exerted by the arterial pressure wave upon the walls of the underlying blood vessel, a speed of propagation of the arterial pressure wave, or shape of the waveform of the arterial pressure wave.
  • These output values may be utilised output as such to the user through a user interface included in or integrated with the device, or they may be delivered to an external server component for further processing .
  • the device 100 may thus comprise, or be connected to an interface unit 130 that comprises at least one input unit for inputting data to the internal processes of the device, and at least one output unit for outputting data from the internal processes of the device.
  • the interface unit 130 typically comprises plug- in units acting as a gateway for information delivered to its external connection points and for information fed to the lines connected to its external connection points.
  • the interface unit 130 typically comprises a radio transceiver unit, which includes a transmitter and a receiver.
  • the transmitter of the radio transceiver unit receives a bit stream from the processing component 108, and converts it to a radio signal for transmission by the antenna.
  • the radio signals received by the antenna are led to the receiver of the radio transceiver unit, which converts the radio signal into a bit stream that is forwarded for further processing to the processing component 108.
  • the interface unit 130 may also comprise a user interface with a keypad, a touch screen, a microphone, and equals for inputting data and a screen, a touch screen, a loudspeaker, and equals for outputting data.
  • the processing component 108 and the interface unit 130 are electrically interconnected to provide means for performing systematic execution of operations on the received and/or stored data according to predefined, essentially programmed processes. These operations comprise the procedures described for the device and the blood pressure information monitoring system.
  • the monitoring system may also comprise a remote node (not shown) communicatively connected to the device 100 attached to the user.
  • the remote node may be an application server that provides a blood pressure monitoring application as a service to a plurality of users.
  • the remote node may be a personal computing device into which a blood pressure monitoring application has been installed .
  • the first signal and the optional second signal have a similar waveform.
  • One may select a reference point from the waveform (e.g. maximum, minimum) and detect occurrence of this reference point in the first signal and in the second signal.
  • a time interval between an instance of the reference point in the waveform of the first signal and an instance of the reference point in the waveform of the second signal corresponds to the time needed by the pressure wave to progress from the first pressure sensor to the second pressure sensor. It is thus possible to compute a speed of propagation of the arterial pressure wave of the user by dividing the predefined sensor distance by the determined time interval. It is known that the speed of the blood pressure wave in a blood vessel may be used to indicate stiffness of the walls of the blood vessel.
  • the shape of the waveform may be used to indicate stiffness of the walls of the blood vessel. For example, it is known that a reflection wave seen close to the peak typically indicates increased stiffness in the blood vessel. It is possible to measure this estimated stiffness by computing from a waveform a value (e.g. the height of the pulse vs. the width of the pulse) and use that to indicate the interesting stiffness characteristic of the arterial pressure wave.
  • a value e.g. the height of the pulse vs. the width of the pulse
  • the noise given in a data sheet of a pressure sensor component SCP1000 of Murata Electronics is 1.5Pa@1.8Hz and 25 ⁇ . This corresponds to a noise density of l. lPa/VHz, which is equivalent to 0.11 mm blood assuming a density of 1 kg/I. If the predefined sensor distance is, for example, 1 cm and the gain factor is 1, a one second measurement gives a calibration error of the order of 1% (standard deviation). This is well adequate for non-invasive blood pressure measurements.
  • the proposed solution provides a user-friendly, stress-minimizing and still accurate method for measuring and monitoring blood pressure information.
  • the configuration is inherently robust, because positioning of the pressure sensors in respect of the artery is not as sensitive to errors as adjusting the elements in the conventional optical arrangements.
  • calibration of the device is quick and easy, and can be implemented without measurements with additional reference equipment.
  • the detected characteristic may be, for example, the detected pressure exerted by the arterial pressure wave upon the walls of the underlying blood vessel. Any measurement arrangement, however, is dependent on the measurement arrangements and conditions. In order to have comparable reference values, the output values need to be calibrated . In the present configuration, calibration is simple and can be performed without additional measurement devices.
  • FIG. 3a and 3b illustrate example embodiments of a sensor arrangement 300.
  • An optional reference capacitor 301 (REF) is located between the first pressure sensor 102 and the optional second pressure sensor 104.
  • the pressure sensors 102, 104 and the reference capacitor 301 may be situated in cavities 302 arranged in the sensor arrangement. Looking from below the cavities may be for example cylindrical, cubical or any other suitable form.
  • the cavities 302 may be filled with a substance like gel etc. to achieve a liquid contact between the tissue and the pressure sensors 102, 104 and the reference capacitor 301 to efficiently convey pulsation.
  • a diaphragm 303 may be arranged to cover the cavity 302. It is to be noted that the sensor arrangement 300 is an example and the number and locations of the pressure sensors and the reference capacitor 301 may vary. There may be more than one pressure sensor 102, 104 and/or reference capacitor in a same cavity 302.
  • FIG. 4 illustrates an example pulse wave with few example points which may be used for blood pressure monitoring .
  • the blood pressure is the pressure the blood exerts against the walls of a blood vessel.
  • the pulse wave, or the pulse pressure wave is the result of the propagation of pressure wave, not blood itself, in the blood vessels. In the cardiac cycle, it is highest during ventricular contraction, or systole, and lowest during ventricular relaxation, or diastole.
  • Systolic blood pressure (SBP) refers to the highest aortic pressure in ventricular contraction, and diastolic blood pressure (DBP) to the lowest aortic pressure after ventricular relaxation and before the opening of the aortic valve.
  • Blood pressure may be reported as millimeter of mercury (mmHg); 1 mmHg equals to about 133,32 pascals.
  • a typical SBP is 120 mmHg and DBP 80 mmHg, or 120/80 mmHg .
  • Valley indicates a position in the pulse wave where the measured pressure is at the lowest, diastolic valley.
  • Peak indicates a position in the pulse wave where the measured pressure is at the highest
  • systolic peak Reflected wave The reflected wave is caused by a d iscontinuity in blood vessels, for example, when larger arteries divide to smaller ones. The discontinuity occurs in multiple sites in the circulatory system, such as in high-resistance arterioles in abdomen, and each site creates a reflected wave which combine to form a single wave.
  • Dicrotic notch is the result of the closure of the aortic valve.
  • the pressure is higher after the dicrotic notch due to capacitive behavior of the aorta : right before the closure of the aortic valve, the blood momentarily flows back to the heart thus lowering the pressure in the aorta; next, as the pressure is lower, the aorta releases stored mechanical energy and pushes blood forward . This creates a pressure wave that amplifies the primary pulse wave.
  • FIG 5 illustrates an example flow chart of a pulse wave measurement process for identifying e.g . the example points illustrated in Figure 4.
  • Receiving pulse wave data 501 from the pressure sensors 102, 104 may include short term or continuous monitoring .
  • the measurement may be real-time or the received pulse wave data may first be stored somewhere and analysed later.
  • the measured pulse wave data may be processed using common signal processing means.
  • the processing 502 may include high-pass filtering for example with a cut-off frequency of 0.1 Hz.
  • the processing 502 may include low pass filtering for example with a cut-off frequency of 30Hz.
  • the processing 502 may also include differentiating the pulse wave data for example once or twice. Between all differentiations the signal can be S-G filtered to minimize noise.
  • Analysing the pulse wave data may include finding a rise 503, finding a valley 504 and finding a peak 505. Based on these findings a start of a pulse can be calculated 506. The pulse wave may be analysed further to find a dicrotic notch 507 and a reflected wave 508. After finding the rise, the peak, the valley and possibly the dicrotic notch and the reflected wave, the pulse may be validated 509 and further desired parameters calculated 510. Using at least the parameters a value for blood pressure can be determined 511.
  • pulse wave parameters can be calculated using the detected characteristics. These pulse wave parameters may include: heart rate or beat-to-beat time, pulse wave velocity, time to systolic peak, time to reflected wave, relative height of the reflected wave, time to dicrotic notch, and relative height of the dicrotic notch etc.
  • Beat-to-beat time can be calculated for example as the time between consecutive rises.
  • the pulse wave velocity can be calculated using the distance between radial and brachial measurement location divided by the time difference between for example rises in the signals.
  • Relative heights can be calculated as a difference between the amplitude of a point and valley in relation to difference between peak and valley.
  • mean values of the pulse wave parameters can be used .
  • other aspects of the pulse can be also measured . These include ensemble averaging of pulses, heart rate variability and pulse pressure variability, standard deviation of heart rate variability and rough estimation of cardiac output.
  • certain user related parameters may be used .
  • Figure 6 illustrates example parameters and corresponding correlation coefficients for pulse wave parameters and person related parameters.
  • the pulse wave parameters and the user related parameters are used to determine the blood pressure of the user.
  • the user related parameters may include user's sex, height (H), weight (W), age, habits like smoking (Not-S) etc.
  • the pulse wave parameters may include pulse wave velocity (PWV), beat to beat (B2B), time to systolic peak (TSP), time to reflective wave (TRW), relative amplitude of the reflective wave (Augl), time to dicrotic notch (TDN), relative amplitude of the dicrotic notch (Did).
  • PWV pulse wave velocity
  • B2B beat to beat
  • TSP time to systolic peak
  • TRW time to reflective wave
  • Taq time to reflective wave
  • TaDN time to dicrotic notch
  • Did relative amplitude of the dicrotic notch
  • the pulse wave velocity (PWV) can be calculated using pulse transit time (PTT) from one pressure sensor to another and the distance between the two pressure sensors.
  • equations for estimating systolic blood pressure SBP and diastolic blood pressure DBP can be created .
  • Example equations are presented below, where URP is the user related parameters combined for simplicity.
  • the PRP can be calculated for example:
  • spi, rwi, ai, dni, and di are coefficients for corresponding measured parameters.
  • DBP Fdbp URP + b 2 * B2B + sp 2 * TSP + rw 2 * TRW + dn 2 * TDN + d 2 * Did
  • b 2 , sp 2 , rw 2 , dn 2 and d 2 are coefficients for corresponding measured parameters.
  • the results for both SBP and DBP can be made more accurate, if the equations are e.g . of power two or three.
  • the coefficients can be optimized by calculating least mean squares between estimation of a blood pressure and reference measurements. Other suitable optimization methods may be used too.
  • DBP kdbp, i * Fdbp + kdbp, 2 * Fdbp 2 + kdbp,3 * Fdbp 3
  • One advance of the current invention is that there is no need to measure absolute blood pressure values. Using the relative values of the parameters and correlative coefficients values representing blood pressure can be determined.
  • the sensor may be any device or a combination of devices that is capable of generating a signal that varies according to deformations of tissue of a subject when an arterial pressure wave expands or contracts a blood vessel underlying the tissue.
  • Figure 7 illustrates an embodiment, where the signal is generated by means of a photoplethysmograph that is configured to optically obtain a volumetric measurement of a blood vessel underlying the tissue.
  • Photoplethysmograph refers here to a device applying an optical measurement technique where a light source 70 sends a first optical signal 72 into the tissue and a light detector 74 reads a second optical signal 76 that corresponds to a backscattered part of the first optical signal.
  • the variation of the second signal may be used as a photoplethysmogram that corresponds with the variation of the blood volume in the blood vessel underlying the tissue. Typically invisible infrared light is applied in the measurement. It has been detected that the photoplethysmogram includes pulse waves, from which pulse wave parameters may be detected as described above.
  • An advantage of the optical embodiment of Figure 8 in view of the pressure sensor implementations is that a photoplethysmograph does not necessitate direct contact with the skin surface, which makes a blood pressure measurement accessory even easier to wear.

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

Abstract

La présente invention concerne un dispositif, un système et un procédé pour surveiller les informations de pression artérielle d'un utilisateur. Un dispositif est configuré avec au moins un capteur, un élément de fixation et un composant de traitement. Dans le procédé, le capteur est fixé de façon détachable à une position sur la surface externe d'un tissu de l'utilisateur. Le capteur génère un signal qui varie en fonction des déformations du tissu en réponse à une onde de pression artérielle dilatant ou contractant un vaisseau sanguin au-dessous du tissu. Le signal est utilisé pour calculer les paramètres d'onde d'impulsion représentant des caractéristiques détectées de l'onde de pression artérielle en progression de l'utilisateur et la valeur de pression artérielle de l'utilisateur.
PCT/IB2014/067110 2013-12-20 2014-12-19 Procédé amélioré de surveillance de la pression artérielle Ceased WO2015092753A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
FI20136306 2013-12-20
FI20136306A FI20136306L (fi) 2013-03-22 2013-12-20 Parannettu verenpaineen seurantamenetelmä

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WO2015092753A1 true WO2015092753A1 (fr) 2015-06-25

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Cited By (3)

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Publication number Priority date Publication date Assignee Title
WO2019155390A1 (fr) * 2018-02-06 2019-08-15 Tarilian Laser Technologies Limited Surveillance continue non invasive de la pression artérielle
EP3917386A1 (fr) * 2019-01-29 2021-12-08 Fresenius Medical Care Deutschland GmbH Procédé de détermination d'une valeur de pression artérielle d'un patient, tensiomètre et système de dialyse
CN118507039A (zh) * 2023-12-19 2024-08-16 荣耀终端有限公司 妊娠期血压风险评估方法、电子设备及可读存储介质

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US20050228299A1 (en) 2004-04-07 2005-10-13 Triage Wireless, Inc. Patch sensor for measuring blood pressure without a cuff
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US20080039731A1 (en) * 2005-08-22 2008-02-14 Massachusetts Institute Of Technology Wearable Pulse Wave Velocity Blood Pressure Sensor and Methods of Calibration Thereof
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US6533729B1 (en) 2000-05-10 2003-03-18 Motorola Inc. Optical noninvasive blood pressure sensor and method
US20050228299A1 (en) 2004-04-07 2005-10-13 Triage Wireless, Inc. Patch sensor for measuring blood pressure without a cuff
NZ539983A (en) * 2005-05-12 2005-11-25 Alexei Sivolapov Cuffless continuous blood pressure and blood pressure wave velocity monitor
US20080039731A1 (en) * 2005-08-22 2008-02-14 Massachusetts Institute Of Technology Wearable Pulse Wave Velocity Blood Pressure Sensor and Methods of Calibration Thereof
US20100210956A1 (en) * 2008-05-23 2010-08-19 Hanbyul Meditech Co., Ltd. Apparatus and method for sensing radial arterial pulses for noninvasive and continuous measurement of blood pressure and arterial elasticity

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Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2019155390A1 (fr) * 2018-02-06 2019-08-15 Tarilian Laser Technologies Limited Surveillance continue non invasive de la pression artérielle
CN111989033A (zh) * 2018-02-06 2020-11-24 胡马疗法有限公司 非侵入式连续血压监测
EP3917386A1 (fr) * 2019-01-29 2021-12-08 Fresenius Medical Care Deutschland GmbH Procédé de détermination d'une valeur de pression artérielle d'un patient, tensiomètre et système de dialyse
EP3917386B1 (fr) * 2019-01-29 2025-03-05 Fresenius Medical Care Deutschland GmbH Procédé de détermination d'une valeur de pression artérielle d'un patient, tensiomètre et système de dialyse
US12290341B2 (en) 2019-01-29 2025-05-06 Fresenius Medical Care Deutschland Gmbh Methods for determining a blood pressure value of a patient, blood pressure monitors and dialysis systems
CN118507039A (zh) * 2023-12-19 2024-08-16 荣耀终端有限公司 妊娠期血压风险评估方法、电子设备及可读存储介质
CN118507039B (zh) * 2023-12-19 2025-04-22 荣耀终端股份有限公司 妊娠期血压风险评估方法、电子设备及可读存储介质

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