Pulse wave velocity measurement method and apparatus based on upper arm sphygmomanometer

Abstract

Embodiments of the present application provide a pulse wave conduction velocity measurement method and device based on an upper arm sphygmomanometer, electronic equipment and storage medium. The method is applied to an upper arm sphygmomanometer provided with a cuff, an electrocardio signal acquisition component and a Korotkoff sound signal acquisition component. The method comprises: after the air bag of the cuff worn on the upper arm of a user is inflated to compress the brachial artery to be closed, acquiring the electrocardio signal collected by the electrocardio signal acquisition component and the Korotkoff sound signal collected by the Korotkoff sound signal acquisition component; analyzing the electrocardio signal of a specified heartbeat cycle to acquire the peak position of the R wave in each heartbeat cycle; analyzing the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle; and calculating the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave. The method improves the measurement accuracy of the pulse wave conduction velocity.

Description

Technical Field

[0001] This application relates to the field of detection technology, and in particular to a method for measuring pulse wave velocity based on an upper arm sphygmomanometer, a device for measuring pulse wave velocity based on an upper arm sphygmomanometer, an upper arm sphygmomanometer, an electronic device, a storage medium, and a computer program product. Background Technology

[0002] Pulse wave velocity is commonly used to assess the degree of arteriosclerosis; higher values ​​indicate poorer vascular elasticity. Therefore, the accuracy of pulse wave velocity measurement is particularly important. Commonly used methods for measuring pulse wave velocity in existing technologies include: carotid-femoral pulse wave velocity measurement, arm-ankle pulse wave velocity measurement, and upper arm oscilloscope method. Among these methods, the carotid-femoral pulse wave velocity measurement method is complex to operate, requires exposure of the patient's private parts (groin), and is highly dependent on the operator's technique, making it difficult to promote in large-scale screening; the arm-ankle pulse wave velocity measurement method involves a large number of peripheral muscular arteries in the measurement path, is easily affected by peripheral vascular resistance, and requires the combination of other indicators, making implementation highly complex; the upper arm oscilloscope method collects pulse waves through the cuff of the measuring device to calculate the conduction time, however, due to the airway integration effect of the 14cm wide cuff, the physical location of the pulse wave (spatial resolution) becomes unclear; and the high-frequency components of the pulse wave transmitted through the long air tube are lost, resulting in a smooth waveform and a large "foot" positioning error (random error can reach 20-30ms), which seriously affects the measurement accuracy.

[0003] It is evident that existing methods for measuring pulse wave velocity still require improvement. Summary of the Invention

[0004] This application provides a method for measuring pulse wave velocity based on an upper arm blood pressure monitor, which can effectively improve the accuracy of pulse wave velocity measurement and is easy to operate.

[0005] Accordingly, this application also provides a pulse wave velocity measurement device based on an upper arm blood pressure monitor, an upper arm blood pressure monitor, an electronic device, a storage medium, and a computer program product to ensure the implementation and application of the above-mentioned pulse wave velocity measurement method.

[0006] To solve the above-mentioned technical problems, this application is implemented as follows:

[0007] In a first aspect, embodiments of this application provide a method for measuring pulse wave velocity based on an upper arm sphygmomanometer, applied to an upper arm sphygmomanometer, the upper arm sphygmomanometer comprising: a cuff with an air bladder, an electrocardiogram signal acquisition component, and a Korotkoff sound signal acquisition component, the method comprising:

[0008] During the deflation phase after the cuff worn by the user on the upper arm is inflated to the point where the cuff compresses and closes the brachial artery, the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal generated by the blood flowing in the brachial artery acquired by the Korotkoff sound signal acquisition component are obtained.

[0009] The electrocardiogram signal of a specified heartbeat cycle is analyzed to obtain the peak position of the R wave in each heartbeat cycle;

[0010] The Korotkoff sound signal is analyzed based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle;

[0011] The pulse wave conduction velocity is calculated based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle.

[0012] Secondly, embodiments of this application provide a pulse wave velocity measurement device based on an upper arm sphygmomanometer, applied to an upper arm sphygmomanometer, the upper arm sphygmomanometer comprising: a cuff with an air bladder, an electrocardiogram signal acquisition component, and a Korotkoff sound signal acquisition component, the device comprising:

[0013] The signal acquisition module is used to acquire the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal generated by the blood flowing in the brachial artery, acquired by the Korotkoff sound signal acquisition component, during the deflation phase after the air bladder of the cuff worn by the user's upper arm is inflated to the point that the cuff compresses and closes the brachial artery.

[0014] The electrocardiogram signal processing module is used to analyze the electrocardiogram signal of a specified heartbeat cycle and obtain the peak position of the R wave in each heartbeat cycle.

[0015] The Korotkoff sound signal processing module is used to analyze the Korotkoff sound signal based on the peak position and determine the arrival time of the Korotkoff sound signal in each heartbeat cycle.

[0016] The pulse wave conduction velocity calculation module is used to calculate the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle.

[0017] Thirdly, embodiments of this application provide an upper arm blood pressure monitor, comprising: a cuff with an air bladder, an electrocardiogram signal acquisition component, a Korotkoff sound signal acquisition component, and a processor, wherein...

[0018] The processor is used to acquire, during the deflation phase after the air bladder of the cuff worn by the user's upper arm is inflated to the point where the cuff compresses and closes the brachial artery, the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal acquired by the Korotkoff sound signal acquisition component, which is generated by the blood flowing in the brachial artery.

[0019] The processor is further configured to analyze the electrocardiogram signal of a specified heartbeat cycle, obtain the peak position of the R wave in each heartbeat cycle, and analyze the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle.

[0020] The processor is further configured to calculate the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each of the heartbeat cycles.

[0021] Fourthly, embodiments of this application provide an electronic device including a processor, a memory, and a program or instructions stored in the memory and executable on the processor, wherein the program or instructions, when executed by the processor, implement the method described in the first aspect.

[0022] Fifthly, embodiments of this application provide a computer-readable storage medium on which a program or instructions are stored, which, when executed by a processor, implement the steps of the method described in the first aspect.

[0023] Compared with the prior art, the embodiments of this application have the following advantages:

[0024] By incorporating an air-filled cuff, an electrocardiogram (ECG) signal acquisition component, and a Korotkoff sound signal acquisition component into an upper arm blood pressure monitor, and during the deflation phase after the cuff inflates to close the brachial artery, the ECG signal acquired by the ECG signal acquisition component and the Korotkoff sound signal generated by blood flowing in the brachial artery acquired by the Korotkoff sound signal acquisition component are obtained. Then, the ECG signal for a specified heartbeat cycle is analyzed to obtain the peak position of the R wave within each heartbeat cycle. Further, the Korotkoff sound signal is analyzed based on the peak position to determine the arrival time of the Korotkoff sound signal within each heartbeat cycle. Finally, based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle, the pulse wave velocity is calculated. This method not only improves the accuracy of pulse wave velocity measurement but is also convenient to operate. Attached Figure Description

[0025] Figure 1 This is a flowchart of the steps of the pulse wave conduction velocity measurement method disclosed in the embodiments of this application;

[0026] Figure 2 This is a schematic diagram of the upper arm blood pressure monitor disclosed in the embodiments of this application;

[0027] Figure 3 This is a schematic diagram of the pulse wave conduction velocity measuring device disclosed in the embodiments of this application;

[0028] Figure 4 A block diagram schematically illustrates an electronic device for performing the method according to this application; and

[0029] Figure 5 A storage unit for holding or carrying program code implementing the method according to this application is illustrated schematically. Detailed Implementation

[0030] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0031] Reference Figure 1 The pulse wave velocity measurement method based on an upper arm blood pressure monitor disclosed in this application includes steps 102 to 108.

[0032] In some alternative embodiments, it can be achieved through methods such as Figure 2 The upper arm blood pressure monitor shown implements the pulse wave velocity measurement method disclosed in the embodiments of this application.

[0033] like Figure 2As shown, the upper arm blood pressure monitor includes: a cuff 202 with an air bladder, an electrocardiogram (ECG) signal acquisition component 204, a Korotkoff sound signal acquisition component 206, and a processor 208. The ECG signal acquisition component 204 is electrically connected to the processor 208, and the Korotkoff sound signal acquisition component 206 is also electrically connected to the processor 208. The ECG signal acquisition component 204 includes, but is not limited to, electrode pads for recording the electrical signals generated by the heart during each heartbeat cycle from the body surface; in this embodiment, these are referred to as "ECG signals." The Korotkoff sound signal acquisition component 206 includes, but is not limited to, a piezoelectric sensor for capturing the acoustic vibrations generated within the blood vessels at the moment blood flow breaks through the blockage. The air bladder's placement in the cuff 202 is described in the prior art for Korotkoff sound electronic blood pressure monitors, and will not be repeated in this embodiment. The Korotkoff sound signal acquisition component 206 is fixedly disposed at the lower edge (distal edge) or upper edge (proximal edge) of the air bladder in the cuff 202. The electrocardiogram signal acquisition component 204 can be set on the main surface of the upper arm blood pressure monitor in a position that is convenient for a person to grasp and touch.

[0034] In some optional embodiments, the upper arm sphygmomanometer further includes an airway and a Korotkoff sound signal transmission line. During operation, the upper arm sphygmomanometer inflates and deflates the cuff through the airway and receives Korotkoff sound signals acquired by the Korotkoff sound signal acquisition component through the Korotkoff sound signal transmission line. The inflation and deflation process of the cuff is described in the prior art for Korotkoff sound-based electronic sphygmomanometers and will not be repeated in this application. On the other hand, the processor acquires the Korotkoff sound signals generated by blood flowing in the brachial artery, collected by the Korotkoff sound signal acquisition component, through the Korotkoff sound signal transmission line.

[0035] The following is combined Figure 2 The specific implementation methods of each step of the pulse wave conduction velocity measurement method based on an upper arm blood pressure monitor disclosed in the embodiments of this application are described in detail.

[0036] Step 102: During the deflation phase after the cuff worn by the user on the upper arm is inflated to the point where the cuff compresses and closes the brachial artery, the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal generated by the blood flowing in the brachial artery acquired by the Korotkoff sound signal acquisition component are obtained.

[0037] For the specific method of inflating and deflating the cuff of the upper arm blood pressure monitor, please refer to the method of inflating and deflating the cuff in the prior art Korotkoff sound electronic blood pressure monitor, which will not be repeated in the embodiments of this application.

[0038] During the use of the upper arm blood pressure monitor, the user touches the ECG signal acquisition component 204 with both hands, wears a cuff on the upper arm, and inflates the cuff until it compresses and closes the brachial artery. Then, the cuff is deflated. At this time, the processor of the upper arm blood pressure monitor controls the ECG signal acquisition component to acquire the user's ECG signal, and controls the Korotkoff sound signal acquisition component to simultaneously acquire the Korotkoff sound signal generated by the blood flowing in the brachial artery. The monitor acquires the user's ECG signal acquired by the ECG signal acquisition component, and the Korotkoff sound signal generated by the blood flowing in the brachial artery acquired by the Korotkoff sound signal acquisition component.

[0039] The specific implementation methods for the ECG signal acquisition component to acquire the user's ECG signal, and the specific implementation methods for the Korotkoff sound signal acquisition component to acquire the Korotkoff sound signal generated by blood flowing in the brachial artery, are all described in the prior art and will not be repeated in the embodiments of this application.

[0040] Step 104: Analyze the electrocardiogram signal of the specified heartbeat cycle to obtain the peak position of the R wave in each heartbeat cycle.

[0041] The specified heart rate cycle refers to the initial specified number of heart rate cycles after the cuff pressure has just fallen below the systolic blood pressure. This specified number can be any integer value from 2 to 6, such as the initial 3 heart rate cycles or the initial 2 heart rate cycles. Preferably, the specified number is any integer value from 3 to 5. During the cuff deflation phase, the Korotkoff sounds (i.e., the first Korotkoff sound) generated in the first few heart rate cycles after the cuff pressure has just fallen below the systolic blood pressure are the strongest, representing the blood flow has just broken through the blockage, and the physical model is the clearest, which helps improve measurement accuracy. This method utilizes the acoustic transient characteristics of the first Korotkoff sound to effectively solve the problem of smooth wave bases and difficulty in accurately locating time points in traditional pressure pulse waves, thereby improving measurement accuracy.

[0042] Optionally, the step of analyzing the electrocardiogram (ECG) signal for a specified heartbeat cycle to obtain the peak position of the R wave within each heartbeat cycle includes: performing bandpass filtering on the ECG signal to obtain a filtered signal; performing R-wave enhancement processing on the filtered signal to construct the energy envelope of the ECG signal; scanning the energy envelope using adaptive dual thresholds to determine an R-wave search time window; searching for the maximum value of the ECG signal within each R-wave search time window to obtain the position of the maximum value; and using the position of the maximum value as the peak position of the R wave within each specified heartbeat cycle.

[0043] The QRS complex is a waveform in an electrocardiogram (ECG) representing ventricular depolarization, reflecting changes in the depolarization potential and time of the left and right ventricles. The first downward wave is the Q wave, the upward wave is the R wave, and the following downward wave is the S wave. The R wave is dominant in lead I. In the embodiments of this application, when using the upper arm blood pressure monitor, the user needs to contact the ECG signal acquisition component 204 with both hands. The upper arm blood pressure monitor acquires the QRS complex in lead I through the ECG signal acquisition component 204.

[0044] The bandpass signal is an electrocardiogram (ECG) signal within a specified frequency range. Optionally, the specified frequency range is an ECG signal between 0.5 and 100 Hz. For example, based on a phase-fidelity filtering strategy, a 0.5-100 Hz bandpass filter is used to bandpass filter the acquired raw ECG signal, resulting in an ECG signal with a frequency between 0.5 and 100 Hz, denoted as the "filtered signal". Using bidirectional zero-phase digital filtering technology to bandpass filter the ECG signal can eliminate filter group delay and ensure that the peak value of the R wave does not shift on the time axis.

[0045] Next, the filtered signal is subjected to R-wave enhancement processing to construct the energy envelope of the electrocardiogram signal.

[0046] Optionally, the step of performing R-wave enhancement processing on the filtered signal to construct the energy envelope of the electrocardiogram signal includes: performing five-point differentiation processing on the filtered signal to obtain a first denoised signal with R-wave enhancement; performing point-by-point squaring signal enhancement processing on the first denoised signal to obtain a second denoised signal with R-wave enhancement; and performing moving window integration processing on the second denoised signal to obtain the energy envelope of the electrocardiogram signal.

[0047] After bidirectional zero-phase filtering from 0.5 to 100 Hz, the resulting filtered signal is pure ECG signal data. Next, the filtered signal is first subjected to five-point differentiation to obtain the first denoised signal with enhanced R-wave. Indicates point The electrocardiogram signal value can be expressed by the five-point differential formula as follows: ,in, This represents the filtered signal at acquisition point n.

[0048] The filtered signal is smoothed using a five-point differential, which allows for smoother slope extraction and reduces high-frequency glitches. The first denoised signal obtained after the five-point differential process highlights the steep rising and falling edges of the R-wave while suppressing the gentle P-wave and T-wave.

[0049] Then, the first denoised signal is subjected to a nonlinear transformation by squaring point by point to obtain the second denoised signal, so as to highlight the energy, amplify the high amplitude R-wave component, and exponentially improve the signal-to-noise ratio.

[0050] Next, the second denoised signal undergoes moving window integration. For example, using the formula:

[0051] For the second denoised signal Perform moving window integration processing, where, Indicates the size of the movable window. This indicates the offset of the sampling points of the second denoised signal. This represents the energy envelope of the electrocardiogram signal at sampling point n.

[0052] Optionally, the step of scanning the energy envelope using adaptive dual thresholds to determine the R-wave search time window includes: scanning the energy envelope from front to back using a first threshold; if the amplitude of the scanned energy envelope is greater than the first threshold, the time position corresponding to the amplitude is taken as the position of a candidate R-wave; if no amplitude of an energy envelope greater than the first threshold is scanned within a specified period, the energy envelope is re-scanned from front to back using a second threshold, and the time position corresponding to the amplitude of the scanned energy envelope greater than the second threshold is taken as the position of a candidate R-wave; a first preset time point before the position of the first candidate R-wave is taken as the start time of the R-wave search time window, and a second preset time point after the last candidate R-wave is taken as the end time of the R-wave search time window, thus obtaining the R-wave search time window. The specified period can be 1.66 times the average RR interval. The RR interval is the time interval between two adjacent R waves on an electrocardiogram.

[0053] In embodiments of this application, a first threshold and a second threshold are dynamically determined based on dynamically determined signal peak levels and noise peak levels. The first threshold is greater than the second threshold. It can be calculated using the following formula = Second threshold It can be calculated using the following formula: ,in, Indicates the peak noise level. Indicates the signal peak level. Indicates the peak noise level.

[0054] In practice, the maximum peak value in the energy envelope of the previous few seconds or the previous complete heartbeat cycle can be taken as a reference value, and 1 / 3 of the reference value can be taken as the signal peak level at the current moment. The value of is taken as 1 / 2 of the reference value as the noise peak level at the current moment. The value of is determined by initializing the noise peak level and signal peak level using the above method, and calculating the first threshold based on the initialized noise peak level and signal peak level, so that the threshold starting point is located in the middle zone between the signal and the noise floor, preventing missed detection due to the threshold being too high or false detection due to the threshold being too low during system cold start.

[0055] Next, the energy envelope of the ECG signal is scanned from front to back. When the amplitude of the scanned energy envelope is greater than the first threshold, it is determined that a candidate QRS wave has been detected. Since the Q wave and S wave have been filtered out in the previous steps, when the amplitude is greater than the first threshold, it can be determined that a candidate R wave has been detected. Furthermore, the time position corresponding to the amplitude is taken as the position of the candidate R wave.

[0056] If no energy envelope amplitude greater than the first threshold is detected within 1.66 times the average RR interval (i.e., no QRS wave is detected within 1.66 times the average RR interval), then the backtracking mode is triggered. Within the current time window, a lower second threshold is used. Rescan the energy envelope of the ECG signal to find R waves that may have been missed due to low amplitude (such as occasional premature ventricular contractions).

[0057] By scanning the energy envelope of the electrocardiogram signal using the method described above, the positions of candidate R waves within the time window corresponding to each heartbeat cycle in the energy envelope can be detected. Optionally, the starting position of the candidate R wave can be defined as the starting point. The endpoint of the candidate R wave is defined as the endpoint. This allows us to obtain a rough time window for each candidate R-wave. , For each coarse time window, extend it forward by a certain time (e.g., 50 milliseconds) to obtain the first preset time point, thus obtaining the R-wave search time window for each candidate R-wave, such as [ , ].

[0058] Then, the raw ECG signal is searched within each R-wave search time window (as described above). The maximum value of the R wave is calculated, and the sampling point n corresponding to the maximum value is recorded. The signal position of sampling point n is used as the peak position of the R wave within the heartbeat cycle corresponding to the current R wave search time window.

[0059] Optionally, after finding the maximum value of the original ECG signal within the R-wave search time window, this method also includes confirming whether the maximum value meets physiological rationality (e.g., >0.25mV) to eliminate misjudgments caused by T-wave elevation and ensure the most critical time reference in pulse wave measurement.

[0060] By using the above method to locate the peak moment of the R wave as the starting point of the cardiac electrical signal, the time quantization error is significantly reduced, ensuring the accuracy of the heart-arm pulse wave conduction velocity calculation.

[0061] Step 106: Analyze the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle.

[0062] Next, the Korotkoff sound signal is analyzed and processed, and the arrival time of the first Korotkoff sound in the corresponding heartbeat cycle is determined based on the peak position of the R wave in each heartbeat cycle, which is taken as the arrival time of the Korotkoff sound signal.

[0063] Optionally, the step of analyzing the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal within each heartbeat cycle includes: performing high-pass filtering and denoising on the Korotkoff sound signal to obtain a denoised discrete Korotkoff sound signal; calculating the TKEO value of each discrete Korotkoff sound signal using the TKEO energy operator (Teager-Kaiser Energy Operator, an algorithm for nonlinear signal processing) to obtain a TKEO value sequence of the Korotkoff sound signal; extracting the envelope of the TKEO value sequence to obtain the energy envelope of the Korotkoff sound signal; determining the envelope segment corresponding to each peak position in the energy envelope based on the peak position; searching in the envelope segment for the first rising edge of the energy envelope with the largest slope exceeding the adaptive noise baseline, as the arrival time of the Korotkoff sound signal within the corresponding heartbeat cycle.

[0064] For example, the Korotkoff sound signal can be high-pass filtered using a 20 Hz high-pass cutoff frequency to effectively filter out low-frequency baseline swaying and limb movement artifacts (typically less than 5 Hz) caused by cuff inflation / deflation. On the other hand, adaptive spectral subtraction is introduced, using silent period sampling to estimate the ambient noise spectrum and subtract it in real time, improving the signal-to-noise ratio of weak Korotkoff sounds. After high-pass filtering and subtraction of the ambient noise spectrum, the denoised discrete Korotkoff sound signal is obtained.

[0065] Optionally, the TKEO value of each of the discrete Korotkoff tone signals can be calculated using the following TKEO energy operator: ,in, This represents the Korotkoff tone signal value at sampling point n. This represents the TKEO energy operator. The TKEO value represents the Korotkow tone signal at sampling point n. The magnitude of the TKEO value indicates the "activity" or rate of change of the signal at the corresponding moment; a larger TKEO value typically corresponds to a moment when the signal amplitude or frequency changes rapidly. In the embodiments of this application, instantaneous abrupt changes in the energy of the Korotkow tone signal can be detected by calculating the TKEO value of the discrete Korotkow tone signal. The TKEO values ​​of the discrete Korotkow tone signal at consecutive sampling points constitute a sequence of TKEO values ​​for the Korotkow tone signal.

[0066] Optionally, the specific implementation methods for extracting the envelope of the TKEO value sequence include, but are not limited to, any combination of one or more methods selected from Hilbert transform, zero-phase low-pass filtering, moving window integration, or peak hold algorithm. In the implementation of this application, the specific implementation method for extracting the envelope of the TKEO value sequence to obtain the energy envelope of the Korotkoff tone signal is not limited.

[0067] Optionally, determining the envelope segment corresponding to each peak position within the energy envelope, based on the peak position, includes: for each peak position, using a position delayed by a first duration as the window start point and a position delayed by a second duration as the window end point, thus obtaining a time window corresponding to the peak position; and using a segment of the energy envelope corresponding to each time window as the envelope segment corresponding to the peak position. The principle for setting the window start point is that it is greater than the sum of the minimum pre-ejection period and the minimum physical transmission time of the pulse wave, to shield against electromagnetic interference and non-blood flow source noise at the moment of R-wave triggering; the principle for setting the window end point is that it covers the maximum theoretical delay of the human body at the lowest pulse wave conduction velocity (e.g., 3 m / s) and is less than the shortest cardiac cycle under high heart rate conditions (e.g., 180 bpm), to prevent false detection across cycles.

[0068] Optionally, the first duration is greater than or equal to 30 milliseconds and less than or equal to 80 milliseconds; the second duration is greater than or equal to 300 milliseconds and less than or equal to 450 milliseconds. Preferably, the first duration is 50 milliseconds and the second duration is 350 milliseconds.

[0069] For example, using the peak time of the R wave in the electrocardiogram signal as a reference, a preset physiological conduction window (e.g., 50ms after the R wave) is added later. Within a 350ms time window, only the first rising edge with the largest slope exceeding the adaptive noise baseline is searched within the energy envelope segment corresponding to the time window, and this rising edge is marked as the arrival time of the first Korotkoff tone signal. The adaptive noise baseline can be determined using, but is not limited to, any of the following methods: First, three times the average energy value of the 20ms preceding the peak position within the time window; second, calculating the average energy value by selecting a silent segment at the end of diastole of the previous heartbeat cycle; third, calculating the median or a specific percentile value of the energy amplitude within the historical time window.

[0070] Then, the energy envelope segment corresponding to each time window is taken as the envelope segment corresponding to the peak position.

[0071] Next, in each envelope segment, the first rising edge of the energy envelope with the largest slope that exceeds the adaptive noise baseline is searched as the arrival time of the Korotkoff tone signal within the corresponding heartbeat cycle.

[0072] Step 108: Calculate the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle.

[0073] Optionally, calculating the pulse wave velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle includes: calculating the signal conduction time within a single heartbeat cycle based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle; obtaining the signal transmission distance within the cuff based on the setting position of the Korotkoff sound signal acquisition component within the cuff and / or the width of the cuff; obtaining the user-matched body surface measurement distance; taking the sum of the signal transmission distance within the cuff and the body surface measurement distance as the total signal transmission distance; and calculating the pulse wave velocity based on the total signal transmission distance and the signal conduction time.

[0074] Optionally, calculating the signal conduction time within a single heartbeat cycle based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle includes: calculating the time difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle; and using the average of the time differences as the signal conduction time within a single heartbeat cycle. For example, the average of the time differences between the arrival time of the Korotkoff sound signal and the peak position of the R wave within 3 to 5 heartbeat cycles can be used as the signal conduction time within a single heartbeat cycle.

[0075] Optionally, obtaining the signal transmission distance within the cuff based on the placement position of the Korotkoff sound signal acquisition component within the cuff and / or the width of the cuff includes: determining that the signal transmission distance within the cuff is zero when the Korotkoff sound signal acquisition component is positioned at the proximal edge of the cuff; and determining that the signal transmission distance within the cuff is the width of the cuff when the Korotkoff sound signal acquisition component is positioned at the distal edge of the cuff. This method, when calculating the signal transmission distance, superimposes the cuff width as a fixed parameter onto the body surface measurement distance to compensate for the systematic physical delay caused by the sensor position. This effectively solves the problem of unclear spatial resolution of the physical location of the pulse wave due to the airway integration effect of a 14 cm wide cuff, thereby improving measurement accuracy.

[0076] Optionally, the user-matched body surface measurement distance is determined based on the user's gender, age, and weight factor. For example, the user-matched body surface measurement distance L1 is calculated using the following formula:

[0077] ,in, This represents the gender factor, with a value of 1 for males and 0 for females. Represents the age factor. This represents the height factor, with values ​​in centimeters.

[0078] Optionally, the pulse wave velocity is calculated based on the total signal transmission distance and the signal conduction time, including: taking the quotient of the total signal transmission distance and the signal conduction time as the pulse wave velocity. As described above, the signal conduction time reflects the time difference between the first Korotkoff sound and the start of the heartbeat cycle. Different vascular conditions affect the magnitude of this time difference. Therefore, based on this time difference, the user's vascular condition can be detected, such as proximal aortic sclerosis.

[0079] Using this method, the user's pulse wave conduction velocity can be obtained.

[0080] In summary, the pulse wave velocity measurement method based on an upper arm sphygmomanometer disclosed in this application is applied to an upper arm sphygmomanometer. The upper arm sphygmomanometer includes a cuff with an air bladder, an electrocardiogram (ECG) signal acquisition component, and a Korotkoff sound signal acquisition component. The method acquires the ECG signal from the ECG signal acquisition component and the Korotkoff sound signal from the blood flowing in the brachial artery from the Korotkoff sound signal acquisition component during the deflation phase after the cuff is inflated to the point of compression of the brachial artery. Then, the method measures the pulse wave velocity for a specified heartbeat cycle. The electrocardiogram (ECG) signal is analyzed to obtain the peak position of the R wave in each heartbeat cycle. Further, the Korotkoff sound signal is analyzed based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle. Finally, based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave in each heartbeat cycle, the pulse wave velocity is calculated. This not only improves the accuracy of pulse wave velocity measurement, but also allows for convenient operation by requiring only the user to touch the ECG signal acquisition component with both hands and wear a cuff on the upper arm.

[0081] Furthermore, this method utilizes the physical characteristic that Korotkoff sound signals are generated at the distal or proximal edge of the cuff to solve the problem of uncertain measurement path length caused by wide cuffs, which helps to improve measurement accuracy.

[0082] Based on the above embodiments, this embodiment also provides a pulse wave velocity measurement device based on an upper arm sphygmomanometer, applied to an upper arm sphygmomanometer, which includes: a cuff with an air bladder, an electrocardiogram signal acquisition component, and a Korotkoff sound signal acquisition component. Figure 3 As shown, the device includes:

[0083] The signal acquisition module 302 is used to acquire the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal generated by the blood flowing in the brachial artery acquired by the Korotkoff sound signal acquisition component during the deflation phase after the air bladder of the cuff worn by the user's upper arm is inflated to the point that the cuff compresses and closes the brachial artery.

[0084] The electrocardiogram signal processing module 304 is used to analyze the electrocardiogram signal of a specified heartbeat cycle and obtain the peak position of the R wave in each heartbeat cycle.

[0085] Korotkoff sound signal processing module 306 is used to analyze the Korotkoff sound signal based on the peak position and determine the arrival time of the Korotkoff sound signal in each heartbeat cycle.

[0086] The pulse wave conduction velocity calculation module 308 is used to calculate the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle.

[0087] Optionally, the pulse wave velocity calculation module 308 is further used for:

[0088] The signal conduction time within a single heartbeat cycle is calculated based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle.

[0089] Based on the location of the Korotkoff sound signal acquisition component within the cuff and / or the width of the cuff, the signal transmission distance within the cuff is obtained;

[0090] Obtain the body surface measurement distance matched by the user;

[0091] The sum of the signal transmission distance within the cuff and the measurement distance on the body surface is taken as the total signal transmission distance;

[0092] The pulse wave propagation velocity is calculated based on the total signal transmission distance and the signal propagation time.

[0093] Optionally, the ECG signal processing module 304 is further configured to:

[0094] The electrocardiogram signal is subjected to bandpass filtering to obtain a filtered signal;

[0095] The filtered signal is subjected to R-wave enhancement processing to construct the energy envelope of the electrocardiogram signal;

[0096] The energy envelope is scanned using an adaptive dual threshold to determine the R-wave search time window;

[0097] The maximum value of the electrocardiogram signal is searched within each of the R-wave search time windows to obtain the location of the maximum value;

[0098] The position of the maximum value is taken as the peak position of the R wave within each specified heartbeat cycle.

[0099] Optionally, the step of performing R-wave enhancement processing on the filtered signal to construct the energy envelope of the electrocardiogram signal includes:

[0100] The filtered signal is subjected to five-point differentiation to obtain the first denoised signal with R-wave enhancement;

[0101] The first denoised signal is subjected to point-by-point squaring signal enhancement processing to obtain the second denoised signal with R-wave enhancement.

[0102] The second denoised signal is subjected to moving window integration processing to obtain the energy envelope of the electrocardiogram signal.

[0103] Optionally, the Korotkoff tone signal processing module 306 is further configured to:

[0104] The Korotkoff tone signal is subjected to high-pass filtering and denoising to obtain a denoised discrete Korotkoff tone signal;

[0105] The TKEO value of each discrete Korotkoff tone signal is calculated using the TKEO energy operator to obtain the TKEO value sequence of the Korotkoff tone signal;

[0106] Envelope extraction is performed on the TKEO value sequence to obtain the energy envelope of the Korotkoff sound signal;

[0107] Based on the peak positions, envelope segments corresponding to each peak position are determined in the energy envelope;

[0108] The first rising edge of the energy envelope with the largest slope exceeding the adaptive noise baseline is searched within the envelope segment, and is taken as the arrival time of the Korotkoff tone signal within the corresponding heartbeat cycle.

[0109] Optionally, determining the envelope segment corresponding to each peak position in the energy envelope based on the peak position includes:

[0110] For each peak position, the position delayed by a first time period is taken as the starting point of the window, and the position delayed by a second time period is taken as the ending point of the window, thus obtaining the time window corresponding to the peak position;

[0111] The segment of the energy envelope corresponding to each time window is taken as the envelope segment corresponding to the peak position.

[0112] The pulse wave velocity measurement device based on an upper arm blood pressure monitor disclosed in this application is used to implement the above-mentioned pulse wave velocity measurement method based on an upper arm blood pressure monitor. For the specific implementation of each module of the device, please refer to the specific implementation of the corresponding steps in the foregoing method embodiments, which will not be repeated here.

[0113] In summary, the pulse wave velocity measurement device based on an upper arm blood pressure monitor disclosed in this application is applied to an upper arm blood pressure monitor. The upper arm blood pressure monitor includes a cuff with an air bladder, an electrocardiogram (ECG) signal acquisition component, and a Korotkoff sound signal acquisition component. During the deflation phase after the cuff is inflated to the point of compression of the brachial artery, the device acquires the ECG signal collected by the ECG signal acquisition component and the Korotkoff sound signal generated by blood flowing in the brachial artery, collected by the Korotkoff sound signal acquisition component. Subsequently, the device measures the pulse wave velocity during a specified heartbeat cycle. The electrocardiogram (ECG) signal is analyzed to obtain the peak position of the R wave in each heartbeat cycle. Further, the Korotkoff sound signal is analyzed based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle. Finally, based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave in each heartbeat cycle, the pulse wave velocity is calculated. This not only improves the accuracy of pulse wave velocity measurement, but also allows for convenient operation by requiring only the user to touch the ECG signal acquisition component with both hands and wear a cuff on the upper arm.

[0114] Furthermore, this device utilizes the physical characteristic that Korotkoff sound signals are generated at the distal or proximal edge of the cuff to solve the problem of uncertain measurement path length caused by wide cuffs, which helps to improve measurement accuracy.

[0115] Based on the above embodiments, this application also discloses an upper arm blood pressure monitor, such as... Figure 2 As shown, the upper arm blood pressure monitor includes: a cuff 202 with an air bladder, an electrocardiogram signal acquisition component 204, a Korotkoff sound signal acquisition component 206, and a processor 208, wherein,

[0116] The electrocardiogram signal acquisition component 204 is used to acquire electrocardiogram signals;

[0117] The Korotkoff sound signal acquisition component 206 is used to acquire the Korotkoff sound signal generated by blood flowing in the brachial artery;

[0118] The processor 208 is used to acquire the electrocardiogram signal acquired by the electrocardiogram signal acquisition component 204 and the Korotkoff sound signal generated by the blood flowing in the brachial artery acquired by the Korotkoff sound signal acquisition component 206 during the deflation phase after the air bladder of the cuff worn by the user's upper arm is inflated to the point where the cuff compresses and closes the brachial artery.

[0119] The processor 208 is further configured to analyze the electrocardiogram signal of a specified heartbeat cycle, obtain the peak position of the R wave in each heartbeat cycle, and analyze the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle.

[0120] The processor 208 is further configured to calculate the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each of the heartbeat cycles.

[0121] For specific implementation details of the signal processing performed by the processor 208, please refer to the specific implementation details of the corresponding steps in the method embodiments above, which will not be repeated here.

[0122] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on its differences from other embodiments. Similar or identical parts between embodiments can be referred to interchangeably. For the apparatus embodiments, since they are fundamentally similar to the method embodiments, the description is relatively simple; relevant parts can be referred to the descriptions in the method embodiments.

[0123] The above provides a detailed description of the pulse wave conduction velocity measurement method and device provided in this application. Specific examples have been used to illustrate the principle and implementation of this application. The description of the above embodiments is only for the purpose of helping to understand the method of this application and its core idea. At the same time, for those skilled in the art, there will be changes in the specific implementation and application scope based on the idea of ​​this application. Therefore, the content of this specification should not be construed as a limitation of this application.

[0124] The device embodiments described above are merely illustrative. The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the modules can be selected to achieve the purpose of this embodiment according to actual needs. Those skilled in the art can understand and implement this without any creative effort.

[0125] The various component embodiments of this application can be implemented in hardware, or as software modules running on one or more processors, or a combination thereof. Those skilled in the art will understand that microprocessors or digital signal processors (DSPs) can be used in practice to implement some or all of the functions of some or all of the components in the electronic device according to the embodiments of this application. This application can also be implemented as a device or apparatus program (e.g., a computer program and computer program product) for performing part or all of the methods described herein. Such an implementation of this application can be stored on a computer-readable medium, or can be in the form of one or more signals. Such signals can be downloaded from an Internet website, provided on a carrier signal, or provided in any other form.

[0126] For example, Figure 4 An electronic device is shown that can implement the methods according to this application. The electronic device may be a PC, mobile terminal, personal digital assistant, tablet computer, etc. The electronic device conventionally includes a processor 410 and a memory 420 communicatively connected to the processor, and program code 430 stored in the memory 420 and executable on the processor 410, which, when executing the program code 430, implements the methods described in the above embodiments. The memory 420 may be a computer program product or a computer-readable medium. The memory 420 may be an electronic memory such as flash memory, EEPROM (Electrically Erasable Programmable Read-Only Memory), EPROM, hard disk, or ROM. The memory 420 has a storage space 4201 for the program code 430 of a computer program for performing any of the method steps described above. For example, the storage space 4201 for the program code 430 may include various computer programs for implementing the various steps in the above methods. The program code 430 is computer-readable code. These computer programs can be read from or written to one or more computer program products. These computer program products include program code carriers such as hard disks, compact discs (CDs), memory cards, or floppy disks. The computer program includes computer-readable code that, when executed on an electronic device, causes the electronic device to perform the methods according to the embodiments described above.

[0127] This application also discloses a computer-readable storage medium storing a computer program thereon, which, when executed by a processor, implements the steps described in this application.

[0128] Such a computer program product can be a computer-readable storage medium, which can have the same characteristics as... Figure 4 The memory 420 in the illustrated electronic device is similarly arranged with storage segments, storage spaces, etc. Program code can be stored, for example, in a compressed form on the computer-readable storage medium. The computer-readable storage medium is typically as shown in the reference... Figure 5 The portable or fixed storage unit is described above. Typically, the storage unit includes computer-readable code 430', which is code read by a processor and, when executed by the processor, implements the various steps in the method described above.

[0129] The terms "an embodiment," "embodiment," or "one or more embodiments" as used herein mean that a particular feature, structure, or characteristic described in connection with an embodiment is included in at least one embodiment of this application. Furthermore, please note that the examples of the phrase "in one embodiment" do not necessarily all refer to the same embodiment.

[0130] Numerous specific details are set forth in the specification provided herein. However, it will be understood that embodiments of this application may be practiced without these specific details. In some instances, well-known methods, structures, and techniques have not been shown in detail so as not to obscure the understanding of this specification.

[0131] In the claims, any reference signs placed between parentheses should not be construed as limiting the claims. The word "comprising" does not exclude the presence of elements or steps not listed in the claims. The word "a" or "an" preceding an element does not exclude the presence of a plurality of such elements. This application can be implemented by means of hardware comprising several different elements and by means of a suitably programmed computer. In a unit claim enumerating several means, several of these means may be embodied by the same item of hardware. The use of the words first, second, and third, etc., does not indicate any order. These words can be interpreted as names.

[0132] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application.

Claims

1. A method for measuring pulse wave velocity based on an upper arm sphygmomanometer, applied to an upper arm sphygmomanometer, characterized in that, The upper arm blood pressure monitor includes: a cuff with an air bladder, an electrocardiogram signal acquisition component, and a Korotkoff sound signal acquisition component; the method includes: During the deflation phase after the cuff worn by the user on the upper arm is inflated to the point where the cuff compresses and closes the brachial artery, the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal generated by the blood flowing in the brachial artery acquired by the Korotkoff sound signal acquisition component are obtained. The electrocardiogram signal of a specified heartbeat cycle is analyzed to obtain the peak position of the R wave in each heartbeat cycle; The Korotkoff sound signal is analyzed based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle. This analysis includes: performing high-pass filtering and denoising on the Korotkoff sound signal to obtain a denoised discrete Korotkoff sound signal; calculating the TKEO value of each discrete Korotkoff sound signal using the TKEO energy operator to obtain a TKEO value sequence; extracting the envelope of the TKEO value sequence to obtain the energy envelope of the Korotkoff sound signal; determining the envelope segment corresponding to each peak position in the energy envelope based on the peak position; and searching within the envelope segment for the first rising edge of the energy envelope with the largest slope exceeding the adaptive noise baseline, which is taken as the arrival time of the Korotkoff sound signal in the corresponding heartbeat cycle. The pulse wave conduction velocity is calculated based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle.

2. The method according to claim 1, characterized in that, The calculation of pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each of the cardiac cycles includes: The signal conduction time within a single heartbeat cycle is calculated based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle. Based on the location of the Korotkoff sound signal acquisition component within the cuff and / or the width of the cuff, the signal transmission distance within the cuff is obtained; Obtain the body surface measurement distance matched by the user; The sum of the signal transmission distance within the cuff and the measurement distance on the body surface is taken as the total signal transmission distance; The pulse wave propagation velocity is calculated based on the total signal transmission distance and the signal propagation time.

3. The method according to claim 1, characterized in that, The analysis of the electrocardiogram signal for a specified heartbeat cycle to obtain the peak position of the R wave within each heartbeat cycle includes: The electrocardiogram signal is subjected to bandpass filtering to obtain a filtered signal; The filtered signal is subjected to R-wave enhancement processing to construct the energy envelope of the electrocardiogram signal; The energy envelope is scanned using an adaptive dual threshold to determine the R-wave search time window; The maximum value of the electrocardiogram signal is searched within each of the R-wave search time windows to obtain the location of the maximum value; The position of the maximum value is taken as the peak position of the R wave within each specified heartbeat cycle.

4. The method according to claim 3, characterized in that, The step of performing R-wave enhancement processing on the filtered signal to construct the energy envelope of the electrocardiogram signal includes: The filtered signal is subjected to five-point differentiation to obtain the first denoised signal with R-wave enhancement; The first denoised signal is subjected to point-by-point squaring signal enhancement processing to obtain the second denoised signal with R-wave enhancement. The second denoised signal is subjected to moving window integration processing to obtain the energy envelope of the electrocardiogram signal.

5. The method according to claim 1, characterized in that, The step of determining the envelope segment corresponding to each peak position in the energy envelope, based on the peak position, includes: For each peak position, the position delayed by a first time period is taken as the starting point of the window, and the position delayed by a second time period is taken as the ending point of the window, thus obtaining the time window corresponding to the peak position; The segment of the energy envelope corresponding to each time window is taken as the envelope segment corresponding to the peak position.

6. A pulse wave velocity measuring device based on an upper arm sphygmomanometer, applied to an upper arm sphygmomanometer, the upper arm sphygmomanometer comprising: The device includes a cuff with an airbag, an electrocardiogram signal acquisition component, and a Korotkoff sound signal acquisition component. The signal acquisition module is used to acquire the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal generated by the blood flowing in the brachial artery, acquired by the Korotkoff sound signal acquisition component, during the deflation phase after the air bladder of the cuff worn by the user's upper arm is inflated to the point that the cuff compresses and closes the brachial artery. The electrocardiogram signal processing module is used to analyze the electrocardiogram signal of a specified heartbeat cycle and obtain the peak position of the R wave in each heartbeat cycle. The Korotkoff sound signal processing module is used to analyze the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle. The step of analyzing the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle includes: performing high-pass filtering and denoising on the Korotkoff sound signal to obtain a denoised discrete Korotkoff sound signal; calculating the TKEO value of each discrete Korotkoff sound signal using the TKEO energy operator to obtain a TKEO value sequence of the Korotkoff sound signal; extracting the envelope of the TKEO value sequence to obtain the energy envelope of the Korotkoff sound signal; determining the envelope segment corresponding to each peak position in the energy envelope based on the peak position; and searching for the first rising edge of the energy envelope with the largest slope exceeding the adaptive noise baseline in the envelope segment as the arrival time of the Korotkoff sound signal in the corresponding heartbeat cycle. The pulse wave conduction velocity calculation module is used to calculate the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each heartbeat cycle.

7. An upper arm blood pressure monitor, characterized in that, include: The system includes an airbag cuff, an electrocardiogram (ECG) signal acquisition unit, a Korotkoff sound signal acquisition unit, and a processor. The processor is used to acquire, during the deflation phase after the air bladder of the cuff worn by the user's upper arm is inflated to the point where the cuff compresses and closes the brachial artery, the electrocardiogram signal acquired by the electrocardiogram signal acquisition component and the Korotkoff sound signal acquired by the Korotkoff sound signal acquisition component, which is generated by the blood flowing in the brachial artery. The processor is further configured to analyze the electrocardiogram signal of a specified heartbeat cycle, obtain the peak position of the R wave in each heartbeat cycle, and analyze the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle. The step of analyzing the Korotkoff sound signal based on the peak position to determine the arrival time of the Korotkoff sound signal in each heartbeat cycle includes: performing high-pass filtering and denoising on the Korotkoff sound signal to obtain a denoised discrete Korotkoff sound signal; calculating the TKEO value of each discrete Korotkoff sound signal using the TKEO energy operator to obtain a TKEO value sequence of the Korotkoff sound signal; extracting the envelope of the TKEO value sequence to obtain the energy envelope of the Korotkoff sound signal; determining the envelope segment corresponding to each peak position in the energy envelope based on the peak position; and searching in the envelope segment for the first rising edge of the energy envelope with the largest slope exceeding the adaptive noise baseline, as the arrival time of the Korotkoff sound signal in the corresponding heartbeat cycle. The processor is further configured to calculate the pulse wave conduction velocity based on the difference between the arrival time of the Korotkoff sound signal and the peak position of the R wave within each of the heartbeat cycles.

8. An electronic device, comprising a memory, a processor, and program code stored in the memory and executable on the processor, characterized in that, When the processor executes the program code, it implements the method according to any one of claims 1 to 5.

9. A computer-readable storage medium having program code stored thereon, characterized in that, When the program code is executed by the processor, it implements the steps of the method described in any one of claims 1 to 5.

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