Aorta type pulse wave conduction velocity measuring device and measuring method

Abstract

The invention provides an aorta type pulse wave conduction velocity measuring device and method, and the method comprises the following steps: binding a blocking cuff of a blood flow blocking module to a to-be-measured artery, binding a simulation cuff of a pulse simulator to the to-be-measured artery, and placing a pulse wave detection sensor at a fingertip or a tiptoe; the blood flow at the artery to be tested is blocked by pressurizing the blocking cuff, and the pressure of the simulation cuff is controlled by the pressure control assembly to simulate and generate pulse waves after the blood flow is blocked; recording a pressure change time point of the pressure control assembly and a starting time point when the pulse wave detection sensor obtains the pulse wave signal; according to the time difference of the two time points and the distance from the extrusion part of the simulated cuff to the pulse wave detection sensor, the pulse wave conduction speed is calculated. According to the method, the manually simulated pulse wave is used as the conduction signal by blocking the blood flow, so that each pulsation is performed in the static arterial duct, and the measurement of the pulse wave conduction velocity is more accurate.

Description

Technical Field

[0001] The present application relates to the field of biomedical engineering, and in particular to an aortic pulse wave velocity measurement device and a measurement method. Background Art

[0002] Pulse Wave Velocity (PWV) refers to the speed at which the pressure fluctuations generated by the heart's contraction and ejection are transmitted in the human arterial system. It can generally be described by the Moens-Korteweg (MK) equation:

[0003]

[0004] Where: PWV is the pulse wave velocity, E0 is the elastic modulus of the blood vessel under no pressure, K and γ are the characteristic parameters of the arterial blood vessels, p is the pressure on the arterial blood vessels, h is the thickness of the blood vessel wall, d is the inner diameter of the blood vessel, and ρ is the density of the blood fluid.

[0005] The above formula shows that the elasticity of arterial blood vessels (elastic modulus E0) is one of the key factors affecting pulse wave velocity (PWV). When other parameters remain unchanged, PWV is proportional to the square root of the vascular elastic modulus E0. The lower the elastic modulus, the greater the compliance of the arterial wall and the slower the propagation speed of the pulse wave; conversely, the higher the elastic modulus, the greater the vascular stiffness and the faster the propagation speed of the pulse wave.

[0006] Since the Moens-Korteweg (MK) equation involves many human characteristic parameters and is difficult to measure, in clinical practice the pulse wave velocity PWV = D / ΔT is generally calculated by measuring the distance between two points (D) and the time difference (ΔT) between the appearance of the pulse wave at the two points.

[0007] In order to measure the pulse wave velocity, there are now a variety of measuring instruments on the market. For example, in the patent No. 201811053282.6, a non-invasive multi-segment peripheral arterial vascular elastic function detection method and instrument are disclosed. By collecting ECG and monitoring point pulse wave signals, the pulse wave velocity of the multi-stage arterial pipeline with the heart as the starting point and the pulse wave detection point as the end point is calculated. The above patent mainly detects the pulse wave generated by the natural beating of the human heart. From the principle of mechanical wave conduction and the MK equation, it can be seen that for the same arterial vascular system, the pulse wave conduction velocity is affected by factors such as vascular elastic modulus, blood pressure, and blood flow. Because blood pressure and blood flow vary greatly with the state of the human body when the heart beats, simply measuring the pulse wave conduction velocity without considering the influence weight of other parameters such as blood pressure will cause the vascular elastic modulus E0 to be distorted, resulting in unstable measurement results, thereby causing large errors in the assessment of the degree of vascular sclerosis and reducing the measurement accuracy. Summary of the invention

[0008] The present application provides an aortic pulse wave velocity measurement device and a measurement method to solve the problems existing in the related art. The technical solution is as follows:

[0009] In a first aspect, an embodiment of the present application provides a method for measuring aortic pulse wave velocity, comprising the following steps:

[0010] Bind the blocking cuff of the blood flow blocking module to the artery to be tested, and bind the simulation cuff of the pulse simulator to the artery to be tested;

[0011] The blood flow at the artery to be tested is blocked by pressurizing the blocking cuff, and after the blood flow is blocked, the pressure of the simulation cuff is controlled by the pressure control component to simulate and generate a pulse wave;

[0012] Record the time point of pressure change of the pressure control component and the starting time point when the pulse wave detection sensor obtains the pulse wave signal;

[0013] The pulse wave conduction velocity is calculated based on the time difference between the pressure change time point and the starting time point of obtaining the pulse wave signal, as well as the distance from the simulated cuff compression site to the pulse wave detection sensor.

[0014] In one embodiment, it further includes:

[0015] The vascular elastic modulus is calculated based on the simulated blood pressure value and the calculated pulse wave velocity.

[0016] In one embodiment, it further includes:

[0017] The pulse wave velocity of the subject is measured multiple times, and the pulse wave velocity and vascular elastic modulus of each measurement are calculated;

[0018] The average values ​​of the plurality of pulse wave velocities and the average values ​​of the plurality of vascular elastic moduli are calculated, and the average value of the plurality of pulse wave velocities is used as the pulse wave velocity of the measured artery of the measurer, and the average value of the plurality of vascular elastic moduli is used as the vascular elastic modulus of the measured artery of the measurer.

[0019] In one embodiment, the blood flow at the artery to be tested is blocked by pressurizing the blocking cuff, and after the blood flow is blocked, the pressure of the simulation cuff is controlled by the pressure control component to simulate and generate a pulse wave, which specifically includes:

[0020] The control panel of the host computer controls the blood flow blocking air pump to pressurize the blocking cuff to a set pressure value, thereby blocking the blood flow at the artery to be tested;

[0021] After the blood flow at the artery to be tested is blocked, the control panel of the host computer controls the inflation and deflation of the simulation cuff through the pressure control component to simulate the generation of a pulse wave at the artery to be tested.

[0022] In a second aspect, an embodiment of the present application provides an aortic pulse wave velocity measurement device, which performs any of the measurement methods described above, and includes:

[0023] A host computer, in which a control panel is arranged;

[0024] A blood flow blocking module is electrically connected to the control board. The blood flow blocking module at least includes a blocking cuff, which blocks the blood flow of the artery to be tested;

[0025] A pulse simulator is electrically connected to the control board. The pulse simulator includes a simulation cuff and a pressure control component. The simulation cuff is connected to the pressure control component. The pressure control component simulates a pulse wave in the artery to be tested through the simulation cuff.

[0026] The pulse wave measurement module is electrically connected to the control board. The pulse wave measurement module at least includes a pulse wave detection sensor. The pulse wave detection sensor can detect the pulse wave of the artery to be tested.

[0027] In one embodiment, the blood flow blocking module also includes a blood flow blocking air pump and a blocking pressure sensor. The blocking cuff has a built-in blocking balloon. The air outlet of the blood flow blocking air pump is connected to the air inlet of the blocking balloon through a blocking catheter. A blocking solenoid valve is externally connected to the blocking catheter. The blood flow blocking air pump and the blocking solenoid valve are electrically connected to the control board respectively; the blocking pressure sensor is externally connected to the blocking catheter, the blocking pressure sensor is placed between the blocking balloon and the blocking solenoid valve, and the blocking pressure sensor is electrically connected to the control board.

[0028] In one embodiment, the pressure control component of the pulse simulator includes a buffer tank, a first pressure control solenoid valve and a second pressure control solenoid valve. The simulation cuff has a built-in simulation balloon. The air outlet of the buffer tank is connected to the air inlet of the simulation balloon through a first simulation catheter. The first pressure control solenoid valve is arranged on the first simulation catheter. The second pressure control solenoid valve is externally connected to the first simulation catheter. The first pressure control solenoid valve and the second pressure control solenoid valve control the inflation and deflation of the simulation balloon. The second pressure control solenoid valve is located between the simulation balloon and the first pressure control solenoid valve. The first pressure control solenoid valve and the second pressure control solenoid valve are both electrically connected to the control board.

[0029] In one embodiment, the pressure control component of the pulse simulator also includes a pressure control sensor, which is externally connected to the first simulation catheter, placed between the simulation balloon and the second pressure control solenoid valve, and electrically connected to the control board.

[0030] In one embodiment, the pressure control component of the pulse simulator also includes a pressure control air pump, the air outlet of the pressure control air pump is connected to the air inlet of the buffer tank through a second simulation catheter, and the pressure control air pump is electrically connected to the control board.

[0031] In one embodiment, the pressure control component of the pulse simulator further includes a third pressure control solenoid valve, the third pressure control solenoid valve is connected to the second simulation catheter, and the third pressure control solenoid valve is electrically connected to the control board.

[0032] The advantages or beneficial effects of the above technical solution include at least:

[0033] When measuring the pulse wave conduction velocity, the present application first blocks the blood flow of the artery to be tested by a blocking cuff, and after the blood flow is blocked, the simulated cuff of the pulse simulator squeezes the blood vessel on the artery to be tested to generate a pulse wave, and the pulse wave is detected by the pulse wave detection sensor. After the pulse simulator is started, the starting time point of the pressure change and the starting time point of the pulse wave detection sensor obtaining the pulse wave signal are recorded, and the pulse wave conduction velocity is calculated according to the distance from the simulated cuff squeezing part to the pulse wave detection sensor and the time difference between the two recorded time points. The present application blocks the blood flow by a blocking cuff, and uses an artificially simulated pulse wave as a conduction signal. The blood pressure, pulse frequency and blood flow are stable and controllable, so that each pulsation is performed in a static artery, which can reduce the interference of the tester's own uncontrollable physiological factors, making the measurement of the pulse wave conduction velocity more accurate, thereby improving the accuracy and stability of the arterial elastic modulus value.

[0034] The above summary is for illustrative purposes only and is not intended to be limiting in any way. In addition to the illustrative aspects, embodiments and features described above, further aspects, embodiments and features of the present application will be readily apparent by reference to the accompanying drawings and the following detailed description. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] In the accompanying drawings, unless otherwise specified, the same reference numerals throughout the multiple drawings represent the same or similar parts or elements. These drawings are not necessarily drawn to scale. It should be understood that these drawings only depict some embodiments disclosed in the present application and should not be regarded as limiting the scope of the present application.

[0036] Figure 1 is a structural diagram of an active pulse wave velocity measurement device of Example 2;

[0037] Figure 2 This is a reference diagram of the active pulse wave velocity measurement device in use according to the second embodiment;

[0038] Figure 3 is a flow chart of the measurement method of embodiment 1;

[0039] Description of reference numerals:

[0040] 1. Host; 11. Control panel; 12. Display screen; 13. Buttons; 2. Blood flow blocking module; 21. Blocking cuff; 22. Blood flow blocking air pump; 23. Blocking balloon; 24. Blocking catheter; 25. Blocking pressure sensor; 26. Blocking solenoid valve; 3. Pulse simulator; 30. First simulation catheter; 31. Simulation cuff; 32. Buffer tank; 33. First pressure control solenoid valve; 34. Second pressure control solenoid valve; 35. Simulation balloon; 36. Pressure control sensor; 37. Pressure control air pump; 38. Third pressure control solenoid valve; 39. Second simulation catheter; 4. Pulse wave measurement module; 41. Pulse wave detection sensor; 42. Fixing component. DETAILED DESCRIPTION

[0041] In the following, only some exemplary embodiments are briefly described. As those skilled in the art will appreciate, the described embodiments may be modified in various ways without departing from the spirit or scope of the present application. Therefore, the drawings and descriptions are considered to be exemplary and non-restrictive in nature.

[0042] Cardiovascular and cerebrovascular diseases have high rates of disability and mortality, which seriously threaten human health. Decreased arterial elasticity and arteriosclerosis caused by various cardiovascular and cerebrovascular risk factors are potential health problems and are precursors to the onset of diseases such as heart failure, renal syndrome, heart disease, and stroke. Therefore, evaluating arterial elasticity (arterial stiffness) and early detection and intervention of the progression of subclinical vascular lesions are of great significance for delaying and controlling cardiovascular and cerebrovascular events. With the advancement of technology and the deepening of clinical research, there are currently many methods for evaluating arteriosclerosis, including invasive methods such as angiography and intravascular ultrasound; non-invasive methods include magnetic resonance imaging, CT scanning, color Doppler ultrasound imaging, pulse wave velocity, etc. Imaging methods are generally used to determine the structural changes of blood vessels, which are often in the late stage of arteriosclerosis and the equipment is expensive. For the early stage of arteriosclerosis without obvious structural changes, pulse wave velocity analysis and other methods are generally used for evaluation. The measurement process has the advantages of simplicity, effectiveness, economy, non-invasiveness, and high repeatability, and has become a common method for clinical diagnosis of arteriosclerosis.

[0043] A large number of clinical studies have shown that pulse wave velocity is an independent predictor of the risk of cardiovascular and cerebrovascular diseases. The pulse wave velocity of healthy people is roughly between 9 and 13 m / s. With the increase of human age and the influence of some risk factors, such as obesity, hypertension, and hyperlipidemia, the stiffness of human arteries increases, the compliance decreases, the elastic reservoir function of the arteries weakens accordingly, and the pulse wave is less absorbed by the blood vessel wall, so the pulse wave conduction velocity in the artery increases. Laurent et al. found that for every 5 m / s increase in PWV, the mortality rate caused by cardiovascular events will increase by 1.51 times; Jacques et al. showed that for every 1 m / s increase in PWV value of patients with end-stage renal disease, the mortality rate caused by different causes will increase by 39%. Therefore, the accuracy of pulse wave velocity has an important impact on the assessment of cardiovascular disease. The European Hypertension Guidelines in 2007 and the Basic Version of the Chinese Hypertension Prevention and Treatment Guidelines in 2009 clearly listed pulse wave velocity as an examination item. In 2021, the Hypertension Branch of the Chinese Geriatrics Society released the "Chinese Expert Consensus on Pulse Wave Velocity Testing for Early Vascular Aging Evaluation", further affirming the importance of pulse wave velocity in the early diagnosis of cardiovascular and cerebrovascular diseases.

[0044] In the existing measurement of pulse wave velocity, it is necessary to calibrate and capture the unknown pulse wave. Therefore, ECG, heart sound and other detection modules are needed to calibrate the occurrence time of the pulse wave. Graphic algorithms are needed to identify the characteristic points of the ECG and pulse waveform to calculate the conduction time of the pulse wave. The remote unstable pulse wave signal needs to be filtered, which increases the complexity and cost of the product. At present, the commonly used measurement method in clinical practice is to use the ECG (electrocardiogram) characteristic point as the pulse wave conduction starting point, and the tension sensor or PPG (photoplethysmography) signal characteristic point as the remote reference point. The product is expensive and requires professional operation, which is not conducive to daily use in a home environment.

[0045] Embodiment 1:

[0046] like Figure 1 , Figure 2As shown, an embodiment of the present application provides an active pulse wave conduction velocity measurement device, which includes: a host 1, in which a control board 11 is arranged; a blood flow blocking module 2, which is electrically connected to the control board 11, and the blood flow blocking module 2 at least includes a blocking cuff 21, and the blood flow of the artery to be tested is blocked by the blocking cuff 21; a pulse simulator 3, which is electrically connected to the control board 11, and the pulse simulator 3 includes a simulation cuff 31 and a pressure control component, and the simulation cuff 31 is connected to the pressure control component, and the pressure control component simulates a pulse wave in the artery to be tested through the simulation cuff 31; a pulse wave measurement module 4, which is electrically connected to the control board 11, and the pulse wave measurement module 4 at least includes a pulse wave detection sensor 41, and the pulse wave detection sensor 41 can detect the pulse wave of the artery to be tested.

[0047] When measuring the pulse wave velocity, the present application first blocks the blood flow of the artery to be tested by blocking the cuff 21, and after the blood flow is blocked, the simulated cuff 31 of the pulse simulator 3 squeezes the blood vessel on the artery to be tested to generate a pulse wave, and the pulse wave is detected by the pulse wave detection sensor 41. After the pulse simulator 3 is started, the starting time point of the pressure change and the starting time point of the pulse wave detection sensor 41 obtaining the signal are recorded, and the pulse wave velocity is calculated according to the distance from the squeezing part of the simulated cuff 31 to the pulse wave detection sensor 41 and the time difference between the two recorded time points. The present application blocks the blood flow by blocking the cuff 21, and uses an artificially simulated pulse wave as a conduction signal. The blood pressure, pulse frequency and blood flow are stable and controllable, so that each pulsation is carried out in a static artery, which can reduce the interference of the tester's own uncontrollable physiological factors, making the measurement of the pulse wave velocity more accurate, thereby improving the accuracy and stability of the arterial elastic modulus value, and providing support for the accurate assessment of vascular sclerosis.

[0048] The host 1 is the control center of the device, and has a display screen 12 and a button 13. The display screen 12 and the button 13 are electrically connected to a control board 11, and the control board 11 is a PCB board. In one embodiment, the host 1 can realize the input and display of the interactive interface, display the measured pulse wave conduction velocity and the elastic modulus of the artery, and can display the continuous change trend of the elastic modulus of the artery on the host.

[0049] In order to achieve blood flow blocking, the blood flow blocking module 2 also includes a blood flow blocking air pump 22. The blocking cuff 21 is built with a blocking balloon 23, and the air outlet of the blood flow blocking air pump 22 is connected to the air inlet of the blocking balloon 23 through a blocking catheter 24. A blocking solenoid valve 26 is externally connected to the blocking catheter 24 through the trachea, and the blood flow blocking air pump 22 and the blocking solenoid valve 26 are electrically connected to the control board 11 respectively. Further, the blood flow blocking module 2 also includes a blocking pressure sensor 25, which can also be externally connected to the blocking catheter 24 through the trachea. The blocking pressure sensor 25 is placed between the blocking balloon 23 and the blocking solenoid valve 26, and the blocking pressure sensor 25 is electrically connected to the control board 11.

[0050] When the blood flow blocking module 2 is in use, the blocking cuff 21 is tied to the root of the upper limb or lower limb of the person to be tested, the blood flow blocking air pump 22 is used to inflate the blocking balloon 23, and the change in air pressure is monitored by the blocking pressure sensor 25. When the air pressure reaches a predetermined pressure value, the inflation is immediately stopped and the blocking electromagnetic valve 26 is closed. When the pulse wave conduction velocity measurement is completed, the blocking electromagnetic valve 26 needs to be opened to quickly discharge the gas in the blocking balloon 23 so that the blood flow of the artery of the upper limb or lower limb can be restored. When the blood flow of the upper limb or lower limb is blocked, a pressure higher than the systolic pressure of 30 mmHg needs to be applied to block the blood flow of the artery to be tested, create a static arterial vascular network, and provide an ideal and stable test environment for pulse wave conduction.

[0051] In order to simulate the pulse wave, the pressure control component of the present application includes a buffer tank 32, a first pressure control solenoid valve 33 and a second pressure control solenoid valve 34. The simulation cuff 31 has a built-in simulation balloon 35, the air outlet of the buffer tank 32 is connected to the air inlet of the simulation balloon 35 through the first simulation catheter 30, the first pressure control solenoid valve 33 is arranged on the first simulation catheter 30, and the second pressure control solenoid valve 34 is connected to the first simulation catheter 30 through the trachea. Further, the second pressure control solenoid valve 34 is located between the simulation balloon 35 and the first pressure control solenoid valve 33. The first pressure control solenoid valve 33 and the second pressure control solenoid valve 34 are both electrically connected to the control board 11.

[0052] The buffer tank 32 inflates the simulated balloon 35 through the first simulated catheter 30. In order to monitor the pressure in the simulated balloon 35, the pressure control assembly of the present application further includes a pressure control sensor 36. The pressure control sensor 36 is connected to the first simulated catheter 30, and the pressure control sensor 36 is placed between the simulated balloon 35 and the second pressure control solenoid valve 34. The pressure control sensor 36 is electrically connected to the control board 11.

[0053] In order to inflate the buffer tank 32, the pressure control assembly further includes a pressure control air pump 37. The air outlet of the pressure control air pump 37 is connected to the air inlet of the buffer tank 32 through the second simulation conduit 39, and the pressure control air pump 37 is electrically connected to the control board 11. In order to control the on and off of the second simulation conduit 39, the pressure control assembly further includes a third pressure control solenoid valve 38. The third pressure control solenoid valve 38 is arranged on the second simulation conduit 39, and the third pressure control solenoid valve 38 is electrically connected to the control board 11.

[0054] Before the blood flow blocking module 2 is used to block the blood flow of the artery to be tested, the first pressure control solenoid valve 33 and the second pressure control solenoid valve 34 are first closed, the third pressure control solenoid valve 38 is opened, and the pressure control air pump 37 is used to inflate the buffer tank 32. When the buffer tank 32 reaches the set pressure value, the third pressure control solenoid valve 38 is closed, and the pressure control air pump 37 stops inflating the buffer tank 32. The set pressure value in the buffer tank 32 can be finely adjusted and determined according to the systolic pressure of the tester, and the pressure in the buffer tank 32 can be measured by a pressure sensor or the like.

[0055] Specifically, the gas storage volume in the buffer tank 32 is determined according to the volume of the simulated balloon 35, ensuring that the pressure drop in the buffer tank 32 is not higher than 10% after the simulated balloon 35 is inflated five times. When the pressure drop in the buffer tank 32 is higher than 10%, the pressure control air pump 37 needs to be started to inflate the buffer tank 32.

[0056] When using the pulse simulator 3 to simulate the pulse wave, firstly, the simulation cuff 31 is tied to the artery to be tested, the first pressure control solenoid valve 33 is opened, and the simulation balloon 35 is inflated through the buffer tank 32, and the pulse wave is generated by squeezing the artery to be tested by the simulation balloon 35. When the simulation balloon 35 is inflated to the set pressure value, the first pressure control solenoid valve 33 is closed, and the second pressure control solenoid valve 34 is quickly opened to discharge the gas in the simulation balloon 35. The inflation frequency and inflation times of the simulation balloon 35 can be set by the host 1. The pulse simulator 3 simulates the process of the heart contracting and ejecting blood to generate a pulse wave by controlling the pressure, frequency and squeezing area of ​​the inflation and deflation of the simulation cuff 31. When the pulse simulator 3 is in use, the simulation cuff 31 is tied to one side of the artery that blocks the blood flow, and the simulation cuff 31 is generally close to the blocking cuff 21.

[0057] The present application uses a pressure-controlled air pump 37 to inflate the buffer tank 32, and provides a stable and large volume of high-pressure gas to the simulated airbag 35 through the buffer tank 32, so as to accelerate the pressure response speed during the inflation and deflation of the simulated cuff 31. In one embodiment, the blocking cuff 21 and the simulated cuff 31 are split structures. In other embodiments, the blocking cuff 21 and the simulated cuff 31 can also be connected to each other, so as to be connected as one.

[0058] In this embodiment, the pulse wave is generated by simulating the inflation and deflation of the cuff 31 to squeeze the blood vessel. In other embodiments, the pulse wave may be generated by other means, such as generating blood pulsation by mechanical squeezing.

[0059] When the pulse simulator 3 is used to simulate the pulse wave, the pulse wave needs to be detected by the pulse wave measuring module 4. The pulse wave measuring module 4 also includes a fixing component 42, and the pulse wave detection sensor 41 is fixed on the fixing component 42. Preferably, the pulse wave detection sensor 41 is a photoplethysmography sensor.

[0060] The fixing component 42 on the pulse wave measurement module 4 is fixed to the end of the fingertip or toe tip to detect the pulse wave arrival signal. In one embodiment, the structure of the fixing component 42 can be similar to a finger sleeve, which is directly sleeved on the end of the fingertip or toe tip. In other embodiments, the fixing component 42 can be an existing finger clip structure, which can be directly clamped on the finger or toe.

[0061] In this embodiment, the pulse wave signal (PPG) is picked up by a photoplethysmography sensor. In other embodiments, tension measurement, oscillometric method, ultrasound imaging, bioimpedance volumetric method, magnetic resonance imaging and other methods can be used to pick up the remote pulse wave signal.

[0062] When the blocking cuff 21 and the simulation cuff 31 are bound to the upper limbs, the pulse wave conduction velocity of the upper limbs is measured. In this case, the brachial artery and the fingertip pulse are used as a combination of measurement points. Since the brachial artery is far away from the fingertips, the time difference in pulse signal conduction is large, the impact of abnormal interference will be reduced, and abnormal values ​​of the pulse wave velocity are less likely to occur. The measurement results are more reliable and stable.

[0063] From the MK equation, we know that during the measurement process, the physical parameters based on blood vessels will not fluctuate in a short period of time; while blood pressure will change with personal emotional state, physical activity and health status, and will fluctuate greatly in an instant. Blood pressure is also one of the key factors affecting pulse wave velocity, so how to reduce the interference of blood pressure is the key to improving measurement accuracy.

[0064] This application simulates an artificial pulse to provide stable and controllable parameters such as blood pressure, pulsation frequency, and pulsating blood flow for the measurement process, making the result of solving the vascular elastic modulus through the MK equation more accurate and stable. At the same time, by controlling the pulsation frequency, the interference of the reflected wave can be reduced and the stability and consistency of the pulse signal can be maintained. In addition, since the artificial pulse wave is controllable, the calibration of the pulse wave and the recognition algorithm of the characteristic points of the equipment can be simplified, thereby providing a more optimized and low-cost measurement method for accurately measuring the pulse wave conduction velocity.

[0065] This application mainly uses artificially controlled pulse waves to measure their conduction velocity in local arterial channels, and then derives the elastic modulus and degree of sclerosis of blood vessels. Active artificial pulse waves can control key parameters that affect the conduction velocity of pulse waves, such as blood pressure, pulsation frequency, and blood flow. By limiting the influence of other factors and maintaining a stable and consistent initial state, the accuracy and stability of the arterial elastic modulus value can be improved, providing support for the accurate assessment of vascular sclerosis.

[0066] Compared with the existing technology, the use of artificially simulated pulse waves as the conduction signal makes the pressure, frequency and blood flow stable and controllable, so that each beat takes place in the static arterial system. This can reduce the interference of reflected waves on the main wave conduction velocity and the interference of the tester's own uncontrollable physiological factors. The use of low-cost photoplethysmography sensors can also complete the accurate measurement of pulse wave signals.

[0067] Since the artificial pulse wave is controllable, the calibration of the unknown pulse wave and the recognition algorithm of the characteristic points can be simplified, the complexity and manufacturing cost of the equipment can be reduced, and a low-cost solution can be provided for the popularization of the application in the home environment. This application can be used for daily arteriosclerosis assessment; due to its multi-parameter control capability, it can also provide support for the in vivo verification of continuous blood pressure measurement technology based on pulse wave conduction velocity.

[0068] The structures of the "blocking cuff 21" and the "simulation cuff 31" of the present application are the same as or similar to the structures of the existing blood pressure cuffs for measuring blood pressure; the "pressure control air pump 37" and the "blood flow blocking air pump 22" are both DC air pumps.

[0069] Embodiment 2:

[0070] like Figure 3 As shown, the present application discloses an active pulse wave conduction velocity measurement method in the following embodiments, and the measurement method includes the following steps: S1: Bind the blocking cuff 21 of the blood flow blocking module 2 to the artery to be measured of the measured person, bind the simulation cuff 31 of the pulse simulator 3 to the artery to be measured, and place the pulse wave detection sensor on the fingertips or toes; S2: Block the blood flow at the artery to be measured by pressurizing the blocking cuff 21, and after the blood flow is blocked, control the pressure of the simulation cuff 31 through the pressure control component to simulate the generation of a pulse wave; S3: Record the pressure change time point of the pressure control component and the starting time point when the pulse wave detection sensor 41 obtains the pulse wave signal; S4: Calculate the pulse wave conduction velocity according to the time difference between the pressure change time point and the starting time point when the pulse wave signal is obtained, and the distance from the compression part of the simulation cuff 31 to the pulse wave detection sensor 41.

[0071] When measuring the pulse wave velocity, the present embodiment first blocks the blood flow of the artery to be tested by blocking the cuff 21. After the blood flow is blocked, the simulated cuff 31 of the pulse simulator 3 squeezes the blood vessel on the artery to be tested to generate a pulse wave, and the pulse wave is detected by the pulse wave detection sensor 41. After the pulse simulator 3 is started, the starting time point of the pressure change and the starting time point of the pulse wave detection sensor 41 obtaining the pulse wave signal are recorded, and the pulse wave velocity is calculated according to the distance from the squeezing part of the simulated cuff 31 to the pulse wave detection sensor 41 and the time difference between the two recorded time points. In the present embodiment, the blood flow is blocked by the blocking cuff 21, and the artificially simulated pulse wave is used as the conduction signal. The blood pressure, pulse frequency and blood flow are stable and controllable, so that each pulsation is performed in a static artery, which can reduce the interference of the tester's own uncontrollable physiological factors, making the measurement of the pulse wave velocity more accurate.

[0072] Among them, in step S1, when measuring the person being measured, the blocking cuff 21 is tied to the root of the upper limb or lower limb, the simulation cuff 31 is tied to the position close to the blocking cuff 21, and the pulse wave detection sensor 41 is worn on the fingertips or toes connected to the upper limb or lower limb. In one embodiment, the pulse wave detection sensor 41 is a photoelectric volumetric pulse wave recording sensor. After the simulation cuff 31 and the pulse wave detection sensor 41 are fixed, it is also necessary to measure the distance D from the compression position of the simulation cuff 31 to the pulse wave detection sensor 41, that is, the distance from the compression position of the simulation cuff 31 to the fingertips or toes.

[0073] After step S1 , parameters such as the tester's account, date, blood flow occlusion time, simulated pulse wave pressure value, pulsation frequency, and pulse wave conduction distance can also be set on the host 1 .

[0074] In step S2, the following steps are specifically included:

[0075] S21: the control panel 11 of the host 1 controls the blood flow blocking air pump 22 to pressurize the blocking cuff 21 to a set pressure value, thereby blocking the blood flow at the artery to be tested;

[0076] S22: After the blood flow at the artery to be measured is blocked, the control panel 11 of the host 1 controls the inflation and deflation of the simulation cuff 31 through the pressure control component to simulate the generation of a pulse wave at the artery to be measured.

[0077] Specifically, the measuring switch is first turned on the host 1, and the control panel 11 of the host 1 controls the blood flow blocking air pump 22 to pressurize the blocking cuff 21 to a set pressure value to block the arterial blood flow of the upper limb or lower limb. The blood flow blocking time is generally controlled within 2 minutes, or adjusted according to clinical research results to ensure the safety of the tester.

[0078] After the arterial blood flow of the upper limb or lower limb is blocked, the pulse simulator 3 is started, and the simulated balloon 35 of the simulated cuff 31 is inflated through the buffer tank 32 of the pulse simulator 3, and the air is quickly exhausted after the inflation reaches the set pressure. The frequency, number of times and air pressure of the inflation in the simulated balloon 35 are all preset, and the pulse wave is simulated by inflation and exhaust.

[0079] Step S3 specifically includes the following steps:

[0080] When the pulse wave is generated by the pulse simulator 3, the pressure is detected by the pressure control sensor 36 on the pulse simulator 3, and the starting time t0 when the pressure control sensor 36 detects the pressure change is recorded. After simulating the generation of the pulse wave, the pulse wave detection sensor 36 can detect the pulse wave signal, and the starting time t1 when the pulse wave detection sensor 36 obtains the pulse wave signal is recorded.

[0081] Step S4 specifically includes the following steps:

[0082] According to the recorded pressure change start time t0 and the pulse wave signal start time t1, the pulse wave conduction time ΔT is calculated: ΔT=t1-t0.

[0083] The pulse wave velocity PWV is calculated based on the pulse wave transmission time ΔT and the distance D: PWV = D / ΔT.

[0084] After step S4, the vascular elastic modulus E0 can also be calculated based on the simulated blood pressure value and the calculated pulse wave velocity. In order to ensure the accuracy of the measurement, the pulse wave velocity of the measured person can be measured multiple times, and the pulse wave velocity and vascular elastic modulus of each measurement can be calculated; the average value of the multiple pulse wave velocities and the average value of the multiple vascular elastic moduli are calculated, and the average value of the multiple pulse wave velocities is used as the pulse wave velocity of the measured artery of the measured person, and the average value of the multiple vascular elastic moduli is used as the vascular elastic modulus of the measured artery of the measured person. Preferably, the average value of 5-10 pulse wave velocities can be taken as the pulse wave velocity, and the average value of 5-10 vascular elastic moduli can be taken as the vascular elastic modulus of the measured person.

[0085] After the measurement is completed, the gas in the blocking cuff 21 needs to be immediately emptied. After the measurement is completed, the measurement result is displayed on the host 1.

[0086] In the description of this specification, the description with reference to the terms "one embodiment", "some embodiments", "example", "specific example", or "some examples" means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present application. Moreover, the specific features, structures, materials or characteristics described may be combined in any one or more embodiments or examples in a suitable manner. In addition, those skilled in the art may combine and combine different embodiments or examples described in this specification and the features of different embodiments or examples, unless they are contradictory.

[0087] In addition, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include at least one of the features. In the description of this application, the meaning of "plurality" is two or more, unless otherwise clearly and specifically defined.

[0088] The above is only a specific implementation of the present application, but the protection scope of the present application is not limited thereto. Any technician familiar with the technical field can easily think of various changes or substitutions within the technical scope disclosed in the present application, which should be included in the protection scope of the present application. Therefore, the protection scope of the present application should be based on the protection scope of the claims.

Claims

1. A method for measuring aortic pulse wave velocity, characterized in that: The following steps are involved: Bind the blocking cuff of the blood flow blocking module to the artery to be tested, bind the simulation cuff of the pulse simulator to the artery to be tested, and place the pulse wave detection sensor on the fingertips or toes; The blood flow at the artery to be tested is blocked by pressurizing the blocking cuff, and after the blood flow is blocked, the pressure of the simulation cuff is controlled by the pressure control component to simulate and generate a pulse wave; Record the time point of pressure change of the pressure control component and the starting time point when the pulse wave detection sensor obtains the pulse wave signal; The pulse wave conduction velocity is calculated based on the time difference between the pressure change time point and the starting time point of obtaining the pulse wave signal, as well as the distance from the simulated cuff compression site to the pulse wave detection sensor.

2. The aortic pulse wave velocity measurement method according to claim 1, characterized in that: Also includes: The vascular elastic modulus is calculated based on the simulated blood pressure value and the calculated pulse wave velocity.

3. The aortic pulse wave velocity measurement method according to claim 2, characterized in that: Also includes: The pulse wave velocity of the subject is measured multiple times, and the pulse wave velocity and vascular elastic modulus of each measurement are calculated; The average values ​​of the plurality of pulse wave velocities and the average values ​​of the plurality of vascular elastic moduli are calculated, and the average value of the plurality of pulse wave velocities is used as the pulse wave velocity of the measured artery of the measurer, and the average value of the plurality of vascular elastic moduli is used as the vascular elastic modulus of the measured artery of the measurer.

4. The aortic pulse wave velocity measurement method according to claim 1, characterized in that: The blood flow at the artery to be tested is blocked by pressurizing the blocking cuff. After the blood flow is blocked, the pressure of the simulation cuff is controlled by the pressure control component to simulate and generate a pulse wave, specifically including: The control panel of the host computer controls the blood flow blocking air pump to pressurize the blocking cuff to a set pressure value, thereby blocking the blood flow at the artery to be tested; After the blood flow at the artery to be tested is blocked, the control panel of the host computer controls the inflation and deflation of the simulation cuff through the pressure control component to simulate the generation of a pulse wave at the artery to be tested.

5. An aortic pulse wave velocity measurement device, characterized in that: The measuring device performs the measuring method according to any one of claims 1 to 4, and the measuring device comprises: A host computer, in which a control panel is arranged; A blood flow blocking module is electrically connected to the control board, and the blood flow blocking module at least includes a blocking cuff, and the blood flow of the artery to be tested is blocked by the blocking cuff; A pulse simulator is electrically connected to the control board, the pulse simulator comprises a simulation cuff and a pressure control component, the simulation cuff is connected to the pressure control component, and the pressure control component simulates a pulse wave in the artery to be tested through the simulation cuff; The pulse wave measurement module is electrically connected to the control board. The pulse wave measurement module at least includes a pulse wave detection sensor. The pulse wave detection sensor can detect the pulse wave of the artery to be tested.

6. The aortic pulse wave velocity measuring device according to claim 5, characterized in that: The blood flow blocking module also includes a blood flow blocking air pump and a blocking pressure sensor. The blocking cuff has a built-in blocking balloon. The air outlet of the blood flow blocking air pump is connected to the air inlet of the blocking balloon through a blocking catheter. A blocking solenoid valve is externally connected to the blocking catheter. The blood flow blocking air pump and the blocking solenoid valve are electrically connected to a control board respectively; the blocking pressure sensor is externally connected to the blocking catheter, the blocking pressure sensor is placed between the blocking balloon and the blocking solenoid valve, and the blocking pressure sensor is electrically connected to the control board.

7. The aortic pulse wave velocity measuring device according to claim 5, characterized in that: The pressure control component of the pulse simulator includes a buffer tank, a first pressure control solenoid valve and a second pressure control solenoid valve. The simulation cuff has a built-in simulation balloon. The air outlet of the buffer tank is connected to the air inlet of the simulation balloon through a first simulation catheter. The first pressure control solenoid valve is arranged on the first simulation catheter. The second pressure control solenoid valve is externally connected to the first simulation catheter. The first control solenoid valve and the second pressure control solenoid valve control the inflation and deflation of the simulation balloon. The second pressure control solenoid valve is located between the simulation balloon and the first pressure control solenoid valve. The first pressure control solenoid valve and the second pressure control solenoid valve are both electrically connected to the control board.

8. The aortic pulse wave velocity measuring device according to claim 7, characterized in that: The pressure control component of the pulse simulator also includes a pressure control sensor, which is externally connected to the first simulation catheter, placed between the simulation balloon and the second pressure control solenoid valve, and electrically connected to the control board.

9. The aortic pulse wave velocity measuring device according to claim 7, characterized in that: The pressure control component of the pulse simulator also includes a pressure control air pump, the air outlet of the pressure control air pump is connected to the air inlet of the buffer tank through a second simulation conduit, and the pressure control air pump is electrically connected to the control board.

10. The aortic pulse wave velocity measuring device according to claim 7, characterized in that: The pressure control component of the pulse simulator further includes a third pressure control solenoid valve, which is connected to the second simulation catheter and electrically connected to the control board.

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