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WO2018113442A1 - Dispositif et un procédé de surveillance continue ambulatoire de la pression artérielle basés sur un transit d'ondes pulsées - Google Patents

Dispositif et un procédé de surveillance continue ambulatoire de la pression artérielle basés sur un transit d'ondes pulsées Download PDF

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WO2018113442A1
WO2018113442A1 PCT/CN2017/110340 CN2017110340W WO2018113442A1 WO 2018113442 A1 WO2018113442 A1 WO 2018113442A1 CN 2017110340 W CN2017110340 W CN 2017110340W WO 2018113442 A1 WO2018113442 A1 WO 2018113442A1
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pulse wave
signal
pwtt
electrocardiographic
blood pressure
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Chinese (zh)
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闵卫东
冯秀丽
潘朋
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Tianjin Puren Onehal Information Technology Co Ltd
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Tianjin Puren Onehal Information Technology Co Ltd
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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 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
    • 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
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6824—Arm or wrist
    • 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

Definitions

  • the invention belongs to the field of non-invasive dynamic blood pressure continuous monitoring technology, and particularly relates to a device and a method for realizing continuous monitoring of dynamic blood pressure by obtaining pulse wave transit time and speed.
  • Cardiovascular and cerebrovascular diseases are the leading cause of death worldwide.
  • the prevalence of cardiovascular disease in China is on the rise.
  • As of the end of 2014 there were approximately 290 million cardiovascular patients in the country (China Cardiovascular Disease Report 2014).
  • Hypertension is the most common cardiovascular disease, with clinical manifestations of increased systemic arterial pressure.
  • Arterial pressure includes systolic blood pressure (SBP) and diastolic blood pressure (DBP), and the mean value of arterial blood pressure during a cardiac cycle is called mean arterial pressure (MAP).
  • SBP systolic blood pressure
  • DBP diastolic blood pressure
  • MAP mean arterial pressure
  • There are many factors that cause hypertension such as heredity (about 40%), disease, or external factors such as nervousness, excessive long-term sodium intake, smoking, obesity, alcoholism, and lack of exercise.
  • Invasive methods mostly require the insertion of a catheter into a blood vessel for continuous monitoring of arterial blood pressure. This method can accurately measure arterial pressure, but the risk factor and the cost of care are high. This method is not a common method.
  • Most non-invasive blood pressure measurement products currently on the market use auscultation (Korotkoff's Sound) and Oscillography. Both methods require wearing an inflatable cuff and applying pressure to the arteries to obtain blood pressure values.
  • the oscillometric method is widely used in electronic sphygmomanometers. After inflation and pressure, the built-in chip and pressure sensing components of the machine make judgments on the changes of the shock wave, and obtain systolic blood pressure and diastolic blood pressure.
  • a blood pressure measurement takes about 1 minute.
  • the size of the cuff for measurement also needs to be replaced according to individual differences, otherwise it will affect the measurement results. Therefore, Existing non-invasive blood pressure measurements are not suitable for hypertensive patients who frequently and repeatedly monitor blood pressure changes over a long period of time. For users who require continuous blood pressure monitoring, long-term pressure on the wearing position can cause localized skin congestion, and the wearer may affect the quality of sleep due to cuff inflation during nighttime use.
  • PWV pulse wave velocity
  • a complete pulse wave is mainly composed of two pressure waves, which are the pressure wave generated by ventricular contraction ejection and the pressure wave generated by the rapid expansion of the ascending aorta by the ascending aorta. Therefore, the pulse wave has the property of mechanical wave and is extremely fast.
  • the speed is transmitted from the heart along the arterial tree.
  • the energy conversion that occurs when the pulse wave is conducted is mainly the energy conversion between the kinetic energy of the pulse wave conduction and the elastic potential energy of the arterial cavity.
  • PWV 2 E h/2r ⁇ (E is Young's modulus, h is the thickness of the artery wall, r is the intravascular radius, ⁇ is Blood density) It can be seen that the Young's modulus represents that the blood vessel elasticity is proportional to PWV and the worse the arterial elasticity is, the faster the pulse wave conduction speed is.
  • PWV blood pressure
  • the radial artery is the more commonly used blood pressure measurement site. Therefore, the calculation of blood pressure using the pulse velocity of the heart to the radial artery is more suitable for the needs of most people.
  • the location of the radial artery is not suitable for long-term wearing of measuring instruments, so the use of the heart-radial artery is more suitable.
  • the brachial artery pulse wave can be obtained by directly measuring the strongest point of the radial artery pulse, and processed together with the ECG signal to obtain the pulse wave conduction velocity.
  • the relationship between changes in Pwv and changes in systolic blood pressure is more obvious, but the feedback on diastolic blood pressure cannot rely solely on pwv. It also needs to consider changes in parameters such as viscous elasticity of blood vessels, blood vessel diameter, blood density, compliance, and swelling. Impact.
  • the Windkessel vascular elastic cavity model provides a suitable theoretical background for changes in vascular parameters.
  • the Windkessel model sees the cardiovascular system as an equivalent circuit.
  • the power source generates a periodic potential difference, which represents the function of the heart, q represents the blood flow;
  • L is the inductance, which represents the inertia of the blood flowing in the artery, and the larger the value, the slower the blood flow velocity and the blood density ⁇ ;
  • R is the electrical resistance, which also represents the microcirculatory system with the greatest peripheral resistance in the cardiovascular cycle;
  • C1 and C2 are capacitors, representing the arterial vessels at all levels, C1 near the current source represents the aorta, C2 represents the arterial branch, and the capacitance value
  • the size reflects the swelling of the blood vessel, and the larger the value, the better the expansion of the blood vessel; on the other hand, hemodynamics proposes the concept of vascular dilatation, which is compatible with the end of the diastolic phase of the arterial vessel.
  • PWV L/PWTT.
  • L is the distance between the two arterial pulse wave detection points
  • PWTT is the pulse wave transit time.
  • the prior art such as the Chinese patent CN100413464C and the German patent DE10061189A1, obtains the PWTT by reflecting the time difference between the landmark points of the heart ejection at the same time for the two-point pulse wave, and directly calculates the blood pressure by using the PWTT instead of the PWV.
  • this method ignores the effect of the distance L between two points of the peripheral measurement point on the blood pressure calculation.
  • the size of L will vary due to individual differences in population. Therefore, only fitting the PWTT to fit the blood pressure value will cause a large error.
  • Inflatable cuff pressurization device cannot achieve true continuous dynamic blood pressure detection
  • Photoelectric components are biased due to factors such as different skin color at the detection site, scars, excessive thickness of the stratum corneum, and tight adhesion to the skin;
  • the pressure sensor obtains the absolute pressure value of the pulse wave, and the method requires high amplitude of the pulse wave, but the signal amplitude is affected by the difference of subcutaneous fat and externally applied pressure, and the accuracy of the result;
  • the problem to be solved by the present invention is to design a continuous dynamic blood pressure monitoring device and method based on pulse wave conduction, and realize continuous dynamic blood pressure monitoring based on pulse wave transit time (PWTT) and pulse wave velocity (PWV), non-invasive and non-inflatable. Cuff, portable, and highly adaptable, accurate and scalable.
  • PWTT pulse wave transit time
  • PWV pulse wave velocity
  • the pulse wave is a waveform formed by cardiac ejection and diastolic pulsation (vibration) propagating along the aorta to the peripheral artery.
  • the heart-phrenic pulse wave velocity refers to the pulse wave of the same cardiac cycle and myocardial beating.
  • the sensor receives the signal change of the brachial artery vascular force, and calculates the relationship between the pulse wave transit time and the heart-to-arterial measurement point distance and the pulse wave conduction velocity, after being processed by the internal computer chip of the sphygmomanometer Measuring the systolic and diastolic blood pressure of the human body, this method can also be used to detect arteriosclerosis between two different arterial measurement points of the human body.
  • a continuous dynamic blood pressure monitoring device based on pulse wave conduction wherein the monitoring device is in the form of a wristwatch, and the main body casing (101) is provided with an electrocardiographic signal acquisition module (104), and the wristband (102) is provided with a wrist artery at the wrist
  • the pulse wave signal acquisition module (103), the ECG signal acquisition module (104) and the pulse wave signal acquisition module (103) are signally connected to the control module (105).
  • control module includes an amplification module (106), a filtering module (107), an AD converter (108), a blood pressure calculation module (109), which are sequentially connected, the amplification module (106) and the ECG signal.
  • the acquisition module (104) is coupled to the pulse wave signal acquisition module (103).
  • the ECG signal acquisition module (104) includes an electrocardiographic upper electrode sheet (201) on the upper cover of the main body case, and an electrocardiographic lower electrode piece (202) and an electrocardiographic ground electrode on the bottom surface of the main body case for closely contacting the skin.
  • the sheet (203), the electrocardiographic upper electrode sheet (201), the electrocardiographic lower electrode sheet (202), and the electrocardiographic ground sheet (203) are connected to the control module (105).
  • the ECG signal acquisition module (104) includes an upper electrode (401) for adhering to the underside of the left clavicle. And a lower electrode (402) above the left nipple, and a transmission line interface (206) on the main body casing (101) connected to the control module (105), the upper electrode (401) and the lower electrode (402) pass An ECG data transmission line (403) is coupled to the transmission line interface (206).
  • the ECG signal acquisition module (104) includes a manual ECG signal acquisition module and an automatic ECG signal acquisition module;
  • the manual ECG signal acquisition module includes an electrocardiographic upper electrode sheet (201) on a cover of the main body case, and an electrocardiographic lower electrode piece (202) and an electrocardiographic ground piece (203) located on the bottom surface of the main body case for closely contacting the skin.
  • the electrocardiographic upper electrode sheet (201), the electrocardiographic lower electrode sheet (202), and the electrocardiographic ground electrode sheet (203) are connected to the control module (105);
  • the automatic electrocardiographic signal acquisition module includes an upper electrode (401) for being placed under the left clavicle and a lower electrode (402) above the left nipple, and is connected to the control module (105) on the main body casing (101).
  • the transmission line interface (206), the upper electrode (401) and the lower electrode (402) are connected to the transmission line interface (206) through an electrocardiographic data transmission line (403), and it should be noted that for the heart on the right side In the human body, the upper electrode (401) is placed just below the right clavicle, and the lower electrode (402) is placed just above the right nipple.
  • a continuous dynamic blood pressure monitoring method based on pulse wave conduction comprising:
  • the diastolic pressure PWTT DBP is calculated based on the systolic pressure PWTT SBP and the duration of the diastolic phase.
  • the interval of acquiring the pulse wave signal in the step (1) is 2 ms.
  • step (2) is:
  • Td The diastolic duration Td [Td0, Td1, ... Tdn] is calculated by the signal s3.
  • PWTT SBP exp(pt1*PWTT)+pt2;
  • pt1, pt2 are fitting parameters that are combined with user-related parameters.
  • PWTT DBP Td * exp ⁇ PWTT SBP / (pt3 ⁇ PWTT) 2 ⁇ - hr1 * heart rate;
  • Td is the length of the diastolic period
  • pt1 and pt2 are the fitting parameters for combining the relevant parameters of the user.
  • a simple monitoring method for continuous dynamic blood pressure calibration values based on pulse wave conduction comprising:
  • the diastolic pressure PWTT DBP is calculated based on the systolic pressure PWTT SBP and the duration of the diastolic phase.
  • the interval between the synchronous acquisition of the ECG signal and the pulse wave signal in the step (1) is 2 ms.
  • step (2) is:
  • PWTT SBP exp(pt1*hrPWTT)+pt2;
  • pt1, pt2 are fitting parameters that are combined with user-related parameters.
  • PWTT DBP Td * exp ⁇ PWTT SBP / (pt3 ⁇ hrPWTT) 2 ⁇ - hr1 * heart rate;
  • Td is the length of the diastolic period
  • pt1 and pt2 are the fitting parameters for combining the relevant parameters of the user.
  • a continuous dynamic blood pressure monitoring method based on pulse wave conduction comprising:
  • the diastolic pressure PWV DBP is calculated based on the systolic pressure PWV SBP and the diastolic duration TD.
  • the personal parameters in the step (1) include a height height, a body weight BMI, an age Age, a smoking condition, and a medication state of the subject.
  • the interval between the synchronous acquisition of the ECG signal and the pulse wave signal in the step (2) is 2 ms.
  • step (3) is:
  • hrPWV (h1*height-5.085)/hrPWTT;
  • PWV SBP gen1 ⁇ sex+pw1 ⁇ hrPWV+bm1 ⁇ BMI+age1 ⁇ age+Sm1*sponder+drug1* medication;
  • gen1, pw1, bm1, age1, Sm1, and drug1 are fitting parameters that combine user-related parameters.
  • step (6) calculates the calculation formula of step (6).
  • the RC 2 value is obtained by fitting the parameters.
  • the present invention has the beneficial effects that the present invention provides a non-invasive continuous blood pressure monitoring device and method, and realizes a miniaturization, portability, no cuff inflation and pressure, and a continuous blood pressure measuring device and method.
  • the device not only does not require a pneumatic cuff to achieve the function of a sphygmomanometer, but also enables long-term continuous monitoring of blood pressure changes, and it can be worn on the wrist like a watch, and can be flexibly applied to various life scenes.
  • the method of continuous blood pressure monitoring of the present invention is based on hemodynamics and the influencing factors of vascular parameters in the vascular elastic cavity model, so that the results of long-term continuous blood pressure measurement are more reliable.
  • FIG. 1 is a schematic structural view of a device in an embodiment of the present invention.
  • Figure 2 is a front elevational view of the wristwatch in the embodiment of the present invention.
  • Figure 3 is a rear view of the wristwatch in the embodiment of the present invention (close to the skin of the wrist);
  • Figure 4 is a cross-sectional view of the device in the embodiment of the present invention worn on the wrist;
  • FIG. 5 is a schematic diagram of manual ECG signal acquisition in the embodiment of the present invention (a calibration operation mode of the simple measurement method);
  • Figure 6 is an accurate measurement wearing diagram (continuous) in the embodiment of the present invention.
  • Figure 7 is a schematic diagram of a left ventricle-aortic PWTT in an embodiment of the present invention.
  • FIG. 8 is a schematic diagram of a pulse wave signal and an electrocardiogram signal in an embodiment of the present invention.
  • FIG. 9 is a schematic diagram of a reduction displacement signal S3 in an embodiment of the present invention.
  • Figure 10 is a diagram showing the definition of the diastolic duration td in the embodiment of the present invention.
  • Figure 11 is a schematic view showing the pulse wave transit time of the heart to the radial artery in the embodiment of the present invention.
  • FIG. 12 is a schematic flow chart of a simple measurement method and a quick calibration simple measurement method in an embodiment of the present invention
  • FIG. 13 is a schematic flow chart of an accurate measurement method in an embodiment of the present invention.
  • FIG. 14 is a schematic diagram of a signal vertex recognition process in an embodiment of the present invention.
  • Fig. 15 is a flow chart showing the calculation of the diastolic duration Td in the embodiment of the present invention.
  • 101 a host shell; 102, a wristband; 103, a pulse wave signal acquisition module; 104, an ECG signal acquisition module;
  • control module 106, amplification module; 107, filter module; 108, AD converter;
  • 109 blood pressure calculation module
  • 110 button control circuit
  • 111 power circuit
  • 112 signal input and output
  • 207 humerus
  • 208 radial artery
  • 209 wrist cross section
  • 301 silicone contact
  • PVDF piezoelectric film 303, sensor housing; 401, upper electrode; 402, lower electrode;
  • the invention establishes a complete mathematical model of the relationship between PWTT, PWV and blood pressure through multiple experimental design and a large number of experimental data fitting, and verifies the relationship between PWTT, PWV and blood pressure, and can realize continuous dynamic blood pressure monitoring.
  • the present invention uses a self-developed "continuous blood pressure monitoring device and method based on pulse wave transit time (PWTT) and pulse wave velocity (PWV)".
  • the pulse wave is a waveform formed by the spread of cardiac ejection and diastolic pulsation (vibration) along the aorta to the peripheral artery.
  • Heart- ⁇ radial pulse wave velocity refers to the speed of the heartbeat pulse wave transmitted to the wrist artery during the same cardiac cycle.
  • the sensor is used to receive the signal changes of the brachial artery vascular force.
  • the systolic blood pressure and diastolic blood pressure of the human body are measured after being processed by the internal computer chip of the sphygmomanometer. This method can also be used to detect arteriosclerosis between two different arterial measurement points in the human body.
  • the device used in the present invention provides two methods for continuous dynamic blood pressure monitoring and a correction method:
  • continuous continuous blood pressure can be obtained by continuously acquiring the pulse wave of a single arterial site (ie, the pulse wave generated by one heartbeat) and decomposing the continuous heart-to-aortic PWTT (fitting the brachial blood pressure value) ).
  • Ii. Accurate monitoring method Continuously acquire the pulse waves of two different arterial beat points at the same time, obtain continuous PWV between the two arteries, and monitor the accurate continuous dynamic blood pressure value (fit the brachial blood pressure value).
  • the present invention provides a rapid correction method for correcting the systolic blood pressure SBP value of a simple measurement method by using a PWTT correction between two different arterial pulse waves by only decomposing a single artery. The accuracy of simple measurement results.
  • the present invention provides a wrist-worn device for non-invasive continuous ambulatory blood pressure detection (shown in Figure 1):
  • the structure of the present invention is shown in FIG. 1 , and the main form of the present invention is a wristwatch, as shown in FIG. 2 and FIG. 3 , which includes a display module 113 , and a main body casing 101 is provided with an electrocardiographic signal acquisition module 104 and a wristband 102 .
  • the dual-channel signals collected by the pulse wave signal acquisition module 103 and the pulse wave signal acquisition module 103 and the pulse wave signal acquisition module 103 pass through each module in the control module 105 (including the amplification module 106, the filter module 107, and the AD converter 108).
  • the blood pressure calculation module 109) obtains a blood pressure value after processing.
  • the present invention is further provided with a button control circuit 110, a power supply circuit 111, and a signal input/output 112 connected to the control module 105.
  • the application example of the present invention uses the pulse-wave transit time (hrPWTT) of the heart-radial artery and its corresponding cardiac-iliac artery pulse wave velocity hrPWV to fit the brachial blood pressure to achieve continuous ambulatory blood pressure monitoring.
  • hrPWTT pulse-wave transit time
  • the acquisition of the arterial pulse wave signal 601 is a prerequisite for calculating the PWTT and PWV.
  • the pulse wave signal acquisition module 103 in this application example includes a pulse wave sensor 204 fastened to the watch band 102, which includes a silicone contact 301, a PVDF piezoelectric film 302 and a sensor housing 303, a connection 204, and a sensor connection line of the control module 105. 205.
  • This application example places the pulse wave sensor 204 in the pulse wave signal acquisition module 103 at the radial artery beat point 208 to obtain a pulse wave signal, that is, a pulse wave 601 of the radial artery (see FIG. 4) by measuring the rate of change of the inner diameter of the artery.
  • the pulse wave sensor (204) in this application example uses a piezoelectric capacitive sensor placed at the radial artery beat point (208) for continuous acquisition of the radial artery pulse wave (601).
  • At least one pulse wave sensor is required to continuously acquire pulse waves of two different arteries at the same time.
  • the pulse wave acquired by this application example is the radial artery pulse wave (501) and the heart pulse wave. Since the heart position is special, the key to measuring the heart pulse wave is to use the ECG signal instead of the pulse wave signal (502).
  • the application center central electrical signal acquisition module (104) includes two sets of electrocardiographic sensors (201-203, 401-402) and an electrocardiographic data transmission line 403, and provides two methods for acquiring ECG signals:
  • Fig. 2 to Fig. 4 using a single lead ECG sensor, including an electrocardiographic upper electrode piece (201) located on the upper surface of the main body case, and an electrocardiographic lower electrode piece (202) located on the bottom surface of the main body case. ) and the electrocardiogram pole piece (203).
  • 202 and 203 are in close contact with the wrist skin, and the other hand touches 201 with any finger to form an electrocardiographic path, and a continuous ECG signal at this moment is obtained, the finger is released, the passage is broken, and the signal is disconnected. (See Figure 5)
  • ECG signal acquisition use chest-mounted ECG sensor, including upper electrode (401) and lower electrode (402), respectively, under the left clavicle and above the left nipple, ECG data transmission line (403)
  • the transmission line interface (206) on the host casing (101) is connected, and the obtained continuous ECG signal can be transmitted to the control module (105) in the host in real time. (See Figure 6)
  • the simple measurement method includes the following points:
  • the key to the simple measurement method is to calculate the pulse wave transit time PWTT (607) transmitted by the pulse wave generated by the cardiac ejection to the aorta.
  • the specific method is to perform a pulse wave (601) of one cycle of acquiring the radial artery. Decomposition, a pulse wave contains the pulse wave (602) generated by left ventricular ejection and the aortic pulse wave (603) formed by aortic compression, calculating the time difference between the two peaks and generating for cardiac ejection.
  • the pulse wave conduction time PWTT (607) transmitted by the pulse wave to the aorta (see Figure 7).
  • Equation 1 The exemplary fitting formula for the systolic pressure PWTT SBP calculation in the simple measurement method is Equation 1:
  • pt1, pt2 are fitting parameters that are combined with user-related parameters, and vary according to changes in individual differences.
  • PWTT DBP Td*exp ⁇ PWTT SBP /(pt3 ⁇ PWTT) 2 ⁇ -hr1*heart rate (Equation 2)
  • Td is the length of diastolic period
  • pt1 and pt2 are the fitting parameters that combine the relevant parameters of the user, and their values change according to the individual differences.
  • the accurate measurement method includes the following points:
  • the key to the accurate measurement method is to calculate the pulse wave transit time hrPWTT transmitted by the pulse wave generated by the cardiac ejection to the radial artery collection point.
  • the specific method is to simultaneously acquire the ECG signal (502) and the radial artery pulse wave (501).
  • the time difference between the calculated R-wave peak in the two-way signal and the valley of the adjacent radial artery pulse wave (501) is hrPWTT.
  • PWV SBP gen1 ⁇ sex+pw1 ⁇ hrPWV+bm1 ⁇ BMI+age1 ⁇ age+Sm1*sponder+drug1* medication
  • gen1, pw1, bm1, age1, Sm1, and drug1 are fitting parameters that combine user-related parameters, and their values change according to individual differences.
  • the present invention provides a method of rapid calibration for simple measurement, that is, using the hrPWTT between the radial artery and the cardiac pulse wave (instead of the electrocardiographic signal), instead of the PWTT obtained by decomposing the radial artery pulse wave in the simple measurement method, Correcting the SBP value of the systolic pressure ensures the accuracy of the simple measurement results.
  • the operation diagram is as shown in FIG. 5, and the process is shown in the flowchart of FIG. 12 in 900-711).
  • the technical solution of the present invention further includes a method for processing the pulse wave signal by the blood pressure calculation module: the signal blood pressure calculation module 109 restores the velocity signal S1 of the pulse waveform signal to the displacement signal S3 (ie, 602) and the displacement signal S3 The method of identifying the peak of each cycle. (Fig. 8, Fig. 9, Fig. 13, Fig. 14)
  • the blood pressure calculation module identifies the apex of the pulse wave signal S1, the main steps of which are shown in Figure 14;
  • the signal analysis processing module normalizes the radial artery pulse wave signal s1 to obtain a pulse wave signal s2;
  • the signal s3 needs to be decomposed using the ⁇ function to obtain the left ventricular pulse wave and the aortic pulse wave recognition, and the peak value of the extracted left ventricular pulse wave and the pulse wave peak of the middle artery are extracted.
  • the valleys V[V 0 , V 1 , ... V n ] of the signal s3 are to be marked.
  • the technical solution of the present invention further includes: a method for extracting a diastolic duration Td[Td0, Td1...Tdn] for each period of the restored displacement signal S3 by the blood pressure calculation module (109) (FIG. 10) .
  • the specific method is shown in Fig. 15; the displacement signal S3 is fitted with the ⁇ function, and the difference signal is calculated to obtain the diastolic duration.
  • the technical solution of the present invention further includes: identifying a time point mark R[R 0 , R 1 , . . . R n ] corresponding to the R wave of the electrocardiogram,
  • the invention provides a non-invasive continuous blood pressure monitoring device and method, and realizes a miniaturization, portability, no cuff inflation and pressure, and a continuous blood pressure measuring device and method.
  • the device not only does not require a pneumatic cuff to achieve the function of a sphygmomanometer, but also enables long-term continuous monitoring of blood pressure changes, and it can be worn on the wrist like a watch, and can be flexibly applied to various life scenes.
  • the method of continuous blood pressure monitoring of the present invention is based on hemodynamics and the influencing factors of vascular parameters in the vascular elastic cavity model, so that the results of long-term continuous blood pressure measurement are more reliable.

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Abstract

La présente invention concerne un dispositif et un procédé de surveillance continue ambulatoire de la pression artérielle basés sur un temps de transit d'ondes pulsées et sur une vitesse de transit d'ondes pulsées. Dans le dispositif de surveillance continue ambulatoire de pression artérielle, un boîtier hôte (101) ayant une forme de montre est équipé d'un module de collecte de signal électrocardiographique (104), un module de collecte de signal d'onde pulsée (103) est placé sur un bracelet (102) à la position faisant face à l'artère radiale du poignet, et le module de collecte de signal électrocardiographique (104) et le module de collecte de signal d'onde pulsée (103) se connectent à un module de commande (105). Le dispositif et le procédé de surveillance continue ambulatoire de pression artérielle peuvent obtenir des ondes pulsées en temps réel, et résoudre le problème de mauvaise acquisition d'onde pulsée cardiaque in vitro. L'invention concerne également un procédé rapide et précis pour obtenir le point temporel d'éjection cardiaque, et le procédé est une partie importante de la surveillance continue ambulatoire de la pression artérielle.
PCT/CN2017/110340 2016-12-21 2017-11-10 Dispositif et un procédé de surveillance continue ambulatoire de la pression artérielle basés sur un transit d'ondes pulsées Ceased WO2018113442A1 (fr)

Applications Claiming Priority (2)

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CN112274126B (zh) * 2020-10-28 2022-11-29 河北工业大学 一种基于多路脉搏波的无创连续血压检测方法、装置
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CN113171067A (zh) * 2021-03-05 2021-07-27 上海立阖泰医疗科技有限公司 一种基于pwv的血压测量方法
CN113288092A (zh) * 2021-05-06 2021-08-24 福建师范大学 一种基于视频提取脉搏波的血压检测方法及终端
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