Carotid artery peripheral blood vessel monitoring method and system

Abstract

The embodiment of the invention provides a carotid artery peripheral blood vessel monitoring method and system.The method comprises the steps that a carotid artery blood vessel is positioned through a probe of transcranial Doppler equipment, the probe is fixed to the corresponding position, and blood flow signals are collected; the probe comprises two array elements, and the two array elements are in a pulse wave PW mode when combined and are in a continuous wave CW mode when separated. After a section of stable blood flow signal is collected, operating power and transmitting power parameters of transcranial Doppler equipment are optimized; and monitoring the quality of the blood flow signal in real time, and if the quality of the blood flow signal is lower than a preset threshold value, performing power parameter optimization again. The power consumption of equipment can be reduced, and long-term monitoring is facilitated; the operation power of the equipment is reduced, the transmitting power is reduced, and the minimum harm to the human body caused by ultrasonic radiation to a subject is reduced.

Description

Technical Field

[0001] This document relates to the field of medical technology, and in particular to a method and system for monitoring carotid peripheral blood vessels. Background Art

[0002] Ultrasonic Doppler blood flow analysis is a method of evaluating the physiological characteristics of different blood flow states through non-invasive examinations. The transcranial Doppler ultrasound blood flow analyzer (abbreviated as transcranial, TCD) is a customized ultrasound device specifically used for transcranial ultrasound examinations. The transcranial is a product that appeared in the early 1980s and is used to diagnose cerebrovascular lesions and help detect conditions such as cerebral vascular narrowing, blockage, poor blood flow, or cerebral hemorrhage. The application of Doppler spectrum analysis technology can provide dynamic waveforms of cerebral blood flow for clinical diagnosis, which is very important for the early detection of cerebrovascular diseases.

[0003] The ultrasonic transcranial Doppler blood flow analyzer uses an external ultrasound probe to transmit ultrasonic waves, which produce the Doppler effect (Doppler frequency shift) of the blood flow and then reflect back to the probe. The analyzer processes the data and obtains the corresponding information.

[0004] The Doppler effect primarily involves the change in the wavelength of radiation emitted by an object due to the relative motion between the source and the observer. In front of the moving source, the waves are compressed, resulting in a shorter wavelength and a higher frequency. Behind the moving source, the opposite effect occurs: the wavelength becomes longer and the frequency becomes lower. The greater the speed of the source, the greater the effect. The degree of frequency change can be used to calculate the source's speed in the direction of observation.

[0005] In certain special situations, such as critical illness and cardiopulmonary resuscitation, prolonged monitoring of a patient's blood flow is necessary. A common monitoring method is carotid artery monitoring. Because the carotid artery is thicker, more engorged with blood, and shallower, with no obstructions, it is well-suited for ultrasound probe monitoring. However, this application places certain demands on the device's size, making the compact and mobile TCD an ideal platform. However, most existing products have fixed transmission power and lack adaptive adjustment mechanisms. Summary of the Invention

[0006] One or more embodiments of this specification provide a method for monitoring carotid artery peripheral blood vessels, including:

[0007] S1. Locate the carotid artery using a transcranial Doppler probe, secure the probe in place, and collect blood flow signals. The probe comprises two array elements, which operate in pulsed wave (PW) mode when combined and in continuous wave (CW) mode when separated.

[0008] S2. After acquiring a stable blood flow signal, optimize the operating power and transmit power parameters of the transcranial Doppler device;

[0009] S3. Monitor the blood flow signal quality in real time. If the blood flow signal quality is lower than the preset threshold, re-implement S2 to optimize the power parameters.

[0010] Furthermore, the probe has a diameter of 0.1 cm to 3 cm, a fixed tilt angle of 30 degrees to 60 degrees, and a focus located outside the carotid artery.

[0011] Furthermore, the carotid artery is located by using the probe of the transcranial Doppler device, and the probe is fixed at the corresponding position to collect blood flow signals. The specific method is as follows:

[0012] The transcranial Doppler device uses CW mode and appropriate power for vascular positioning;

[0013] After the blood flow signal is found, the probe is moved in a small range near the blood flow signal to obtain the best position for the probe, and the probe is fixed to continuously obtain the blood flow signal.

[0014] Furthermore, after collecting a stable blood flow signal, the operating power and transmission power of the transcranial Doppler device are optimized as follows:

[0015] Switch the transcranial Doppler device to PW mode and use a larger volume to ensure that blood flow signals are obtained and that distance accumulation is performed within a range of 1 cm to 2 cm in the carotid artery depth.

[0016] Determine the blood flow direction of the carotid artery, filter out negative blood flow through a complex frequency filter, and use the M-wave signal to optimize the optimal depth;

[0017] When the probe's transmission mode frequently switches between PW and CW modes, an adaptive noise estimation algorithm is used to estimate the background noise of the blood flow signal. The algorithm automatically adjusts and calculates the corresponding background noise according to different modes.

[0018] Optimize the scale and baseline of the sampling rate, optimize the sampling volume and emission voltage, optimize the spectrum signal-to-noise ratio, and reduce the emission power.

[0019] Furthermore, the optimized sampling volume is specifically:

[0020] The blood flow distribution in the scanning depth direction is obtained through the M wave, and the optimal sampling volume is obtained after deconvolution of the blood flow distribution; the blood flow distribution is the result of the convolution of the sampling volume and the blood vessel diameter.

[0021] Furthermore, the specific method of using the adaptive noise estimation algorithm to estimate the background noise of the blood flow signal when switching between PW and CW is:

[0022] First, all data are divided into two categories. If the spectrum contains only noise and the noise is divided into two categories, the distance between the class centers is used to determine whether to merge them. If the variance of the noise class is large, the noise class is further decomposed into two categories.

[0023] The adaptive noise estimation algorithm is used to perform two-category decomposition of noise classes 3-4 times.

[0024] Furthermore, the method further comprises:

[0025] The AD sampling circuit of the transcranial Doppler device is controlled to only collect signals within the sampling volume, further reducing system power consumption.

[0026] One or more embodiments of this specification provide a carotid artery peripheral blood vessel monitoring system, including:

[0027] Vascular positioning module: used to locate the carotid artery using the probe of the transcranial Doppler device, fix the probe in the corresponding position, and collect blood flow signals; the probe includes two array elements, which operate in pulse wave (PW) mode when combined and in continuous wave (CW) mode when separated;

[0028] Power optimization module: used to optimize the operating power and transmission power parameters of the transcranial Doppler device after collecting a stable blood flow signal;

[0029] Monitoring and adjustment module: used to monitor the quality of blood flow signals in real time. If the quality of blood flow signals is lower than the preset threshold, the power parameters are optimized again through the power optimization module.

[0030] One or more embodiments of this specification provide an electronic device, including:

[0031] processor; and,

[0032] A memory is arranged to store computer-executable instructions, which, when executed, cause the processor to implement the steps of the above-mentioned method for monitoring the carotid peripheral blood vessels.

[0033] One or more embodiments of the present specification provide a storage medium for storing computer-executable instructions, which, when executed, implement the steps of the above-mentioned method for monitoring carotid peripheral blood vessels.

[0034] Long-term monitoring of peripheral blood vessels such as the carotid artery using the embodiments of the present invention can reduce device power consumption, which is beneficial for long-term monitoring; it can also reduce device operating power, reduce transmission power, and minimize the harm caused by ultrasonic radiation to the subject's human body.

[0035] The above description is only an overview of the technical solution of the present invention. In order to more clearly understand the technical means of the present invention, it can be implemented in accordance with the contents of the specification. In order to make the above and other purposes, features and advantages of the present invention more obvious and easy to understand, the specific implementation methods of the present invention are specifically listed below. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] In order to more clearly illustrate one or more embodiments of this specification or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments recorded in this specification. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0037] Figure 1 A flowchart of a method for monitoring carotid peripheral blood vessels provided in one or more embodiments of this specification;

[0038] Figure 2 A schematic diagram of the composition of a transcranial Doppler device for a method of monitoring carotid peripheral blood vessels provided in one or more embodiments of this specification;

[0039] Figure 3 A schematic diagram of a transcranial Doppler spectrum of a method for monitoring carotid peripheral blood vessels provided in one or more embodiments of this specification;

[0040] Figure 4 A schematic diagram of the positions of the probe and the aorta in a method for monitoring carotid peripheral blood vessels provided in one or more embodiments of this specification;

[0041] Figure 5 A schematic diagram of background noise classification for a method for monitoring carotid peripheral blood vessels provided in one or more embodiments of this specification;

[0042] Figure 6 A schematic diagram illustrating the effect of the sampling rate on the spectrum of a method for monitoring carotid peripheral blood vessels provided in one or more embodiments of this specification;

[0043] Figure 7 A schematic diagram of the composition of a carotid artery peripheral vascular monitoring system provided in one or more embodiments of this specification;

[0044] Figure 8 A schematic diagram of the structure of an electronic device provided in one or more embodiments of this specification. DETAILED DESCRIPTION

[0045] In order to enable those skilled in the art to better understand the technical solutions in one or more embodiments of this specification, the technical solutions in one or more embodiments of this specification will be clearly and completely described below in conjunction with the drawings in one or more embodiments of this specification. Obviously, the described embodiments are only part of the embodiments of this specification, not all of the embodiments. Based on one or more embodiments of this specification, all other embodiments obtained by ordinary technicians in this field without making creative efforts should fall within the scope of protection of this document.

[0046] Method Example

[0047] According to an embodiment of the present invention, a method for monitoring carotid peripheral blood vessels is provided. Figure 1 A flow chart of a method for monitoring carotid peripheral blood vessels provided in one or more embodiments of this specification, such as Figure 1 As shown, the method for monitoring the carotid peripheral blood vessels according to an embodiment of the present invention specifically includes:

[0048] S1. Locate the carotid artery using a transcranial Doppler probe, secure the probe in place, and collect blood flow signals. The probe includes two array elements, which operate in pulse wave (PW) mode when combined and in continuous wave (CW) mode when separated.

[0049] The transcranial Doppler device consists of emission control, driver, probe base, probe, amplifier, AD sampling, demodulation, signal processing and display sound module, such as Figure 2 As shown in the figure, the transmission control provides a specific transmission signal, which is transmitted at a certain frequency. The driver converts the transmission signal into high voltage, driving the probe to perform electrical-to-acoustic conversion. The probe base is the physical connection between the host and the probe, and the same host can generally connect to multiple different probes. Ultrasonic waves are sent into human tissue, and some energy returns to the probe. The probe then undergoes acoustic-to-electrical conversion, converting the echo containing tissue information back into an electrical signal. The amplifier converts the weak electrical signal into a stronger one, and then the analog-to-digital sampling circuit converts the analog signal into a digital signal. The demodulation and signal processing module removes useless noise from the echo signal, retaining only the valid Doppler signal, which is ultimately converted into image and sound feedback to the operator.

[0050] Depending on the transmission method, there are two transmission modes: PW and CW. In CW mode, signal transmission is continuous. In PW mode, there are intervals between signal transmissions. In PW mode, the device probe uses a single array element with a range gating function. PW mode can measure blood flow velocity at a specific depth and locate and quantitatively analyze blood flow at different depths. In CW mode, the device probe uses two array elements, one for transmitting and one for receiving signals. It does not have range gating capability. CW mode measures the combined Doppler shift of all red blood cells in the acoustic beam path and cannot determine the specific location of blood flow. When measuring in PW mode, parameters such as the size, position, and depth of the sampling volume must be set to ensure measurement accuracy. At the same time, the pulse repetition frequency must be adjusted according to the blood flow velocity to avoid spectral aliasing. When measuring in CW mode, generally only basic parameters such as gain and filtering need to be adjusted, making instrument setup relatively simple.

[0051] Each transmission of a PW signal is equivalent to a sample on the time axis. This transmission frequency is the sampling rate (Fs). The collected raw data is a one-dimensional signal f(t) that varies with time. Doppler signals are inherently non-stationary, exhibiting frequency-domain characteristics, and their frequency varies with time. For continuously transmitted CW signals, when converting them to digital signals for processing or storage, the sampling rate depends on the performance of the sampling analog-to-digital converter used. The sampling rate of CW signals can be several times higher than that of PW signals. As long as basic sampling conditions are met, CW signals are not significantly affected by sampling rate variations. However, due to the pulsed nature of PW signals, the sampling rate requirements are more stringent.

[0052] The power spectrum is usually calculated by fast Fourier transform, which converts each power spectrum into a display line. The power spectrum is converted into an image that is easy for the human eye to recognize through pseudo-color mapping. Usually, the brightness distribution of the spectrum reflects the distribution of blood flow velocity in the blood vessels. Multiple power spectra over a period of time are combined to generate a three-dimensional image with the horizontal axis as the time axis, the vertical axis as the frequency, and the brightness representing the energy intensity. Figure 3 A typical image of an artery is shown.

[0053] In this embodiment, the peripheral blood vessels of the carotid artery are monitored. In order to facilitate the fixation of the probe on the carotid artery, the probe is designed in this embodiment. First of all, the probe volume should not be too large. The traditional linear array ultrasound probe is too long and cannot fit the neck well. At the same time, the probe volume should not be too small. A too small volume will result in a too small sound field range, and it will take more time to search for blood vessels. In addition, if the probe array element area is too small, the sensitivity will be lost, so a slightly larger probe is used. In order to facilitate the fixation of the probe on the carotid artery, the probe of this embodiment uses two array elements. When the two array elements are separated, they support CW mode, and when the two array elements are merged, they can support PW mode. When the two array elements are merged, the sound field range is larger than that of a single array element, so the PW mode can obtain more signals than the CW mode.

[0054] Since the carotid artery and the neck are almost parallel, if the probe is placed directly, the probe will be perpendicular to the blood vessel, and the Doppler examination effect will be poor. In this embodiment, the probe diameter is set to 0.1cm-3cm, and the fixed tilt angle range is designed to be 30 degrees-60 degrees, and the probe focus is located outside the carotid artery. Figure 4 shown.

[0055] Use the transcranial Doppler probe to locate the carotid artery, fix the probe in the corresponding position, and collect blood flow signals. The specific method is as follows:

[0056] The probe is placed just above the patient's neck blood vessels, using CW mode and setting appropriate power to locate the blood vessels; after searching for the blood flow signal, the probe is moved in a small range near the blood flow signal to obtain the optimal position for probe placement, and the probe is fixed to continuously obtain the blood flow signal.

[0057] S2. After acquiring a stable blood flow signal, optimize the operating power and transmission power parameters of the transcranial Doppler device.

[0058] Combine the two array elements of the transcranial Doppler probe, switch to PW mode, use a larger volume, and perform distance accumulation within the carotid artery depth range of 1cm-2cm to ensure that blood flow signals are obtained;

[0059] The blood flow direction of the carotid artery is determined, negative blood flow is filtered out by a complex frequency filter, and the optimal depth is optimized using the M-wave signal.

[0060] In blood flow signal detection, when the probe's transmission mode frequently switches between PW and CW modes, an adaptive noise estimation algorithm is used to estimate the background noise of the blood flow signal. It can automatically adjust and calculate the corresponding background noise according to different modes. In this embodiment, all data are first divided into two categories. When the spectrum contains only noise, the noise is divided into two categories. The center distance of the class is used for judgment. If the distance is too close, it can be merged into one class. Figure 5 As shown in A. In most cases, the spectrum contains only one blood vessel and background noise, and two categories can solve the problem, such as Figure 5 As shown in B; however, in a few complex cases, the noise class in Class 2 may contain some signals and noise, such as Figure 5 As shown in Figure C, the variance of the noise class will be large at this time. In this case, the noise class can be further decomposed into two categories, and the misclassified signals can be extracted separately to ensure the correct calculation of the noise signal. If the noise variance is still large, the two-category decomposition process can be iteratively repeated. In the ultrasonic spectrum, all classes can be exhausted by 3-4 decompositions to correctly separate the noise.

[0061] Then the scale and baseline of the sampling rate are optimized. The scale is the velocity range determined by the sampling rate. For example, if the scale is set to 100cm / s, it usually means that the blood flow velocity range that can be measured is from -100cm / s to 100cm / s. The baseline is a parameter related to the scale height. By adjusting the position of the baseline, the spectrum display effect is more in line with the operator's observation habits. For example, if the scale is set to 100cm / s, when the baseline is set to 0, the blood flow velocity range is from -100cm / s to 100cm / s. Due to the principle of FFT, time domain extraction is equal to frequency domain repetition, so its spectrum is periodic. By adjusting the baseline position, such as setting the blood flow velocity range to -50cm / s to 150cm / s, the positive spectrum and negative spectrum can be set to display range separately, making full use of the effective sampling range and avoiding invalid sampling. According to the sampling law, the sampling rate Fs is proportional to the range that the power spectrum can analyze; if Fs is increased, the analysis range will increase synchronously. When the Fs sampling rate is insufficient, such as Figure 6 As shown in A, Fs needs to be increased to exceed the actual maximum blood flow velocity in order to identify the correct spectrum; when the Fs sampling rate is sufficient, but the baseline setting is unreasonable, such as Figure 6 As shown in B, due to the aliasing effect, the highest blood flow velocity still cannot be correctly identified; when the Fs sampling rate is sufficient and the baseline setting is reasonable, such as Figure 6 As shown in Figure C, the aliasing problem is resolved and the integrity of blood flow can be displayed normally. Therefore, by optimizing the scale and depth, the acquisition of noise can be reduced and the blood flow image can be obtained using the lowest power.

[0062] Transmit power can be further reduced by optimizing the sampling volume and transmit voltage. The optimal sampling volume is obtained by sampling the center of the vessel, omitting the vessel wall and tissue, to achieve the best signal-to-noise ratio. Blood flow distribution and vessel diameter along the scanning depth are determined using the M wave. Deconvolution of the blood flow distribution results in the optimal sampling volume; the blood flow distribution is the product of the convolution of the sampling volume and the vessel diameter. In extreme cases, the AD sampling circuit of the transcranial Doppler device can be controlled to only acquire signals within the sampling volume, temporarily ignoring signals outside the sampling volume, further reducing system power consumption.

[0063] After determining the scale, baseline, depth, and volume, the transmit voltage is finally optimized to ensure the minimum effective signal-to-noise ratio, which can effectively reduce the transmit power.

[0064] S3. Monitor the blood flow signal quality in real time. If the blood flow signal quality is lower than the preset threshold, re-implement S2 to optimize the power parameters.

[0065] The beneficial effects of the present invention are as follows:

[0066] Long-term monitoring of peripheral blood vessels such as the carotid artery using the embodiments of the present invention can reduce device power consumption, which is beneficial for long-term monitoring; it can also reduce device operating power, reduce transmission power, and minimize the harm caused by ultrasonic radiation to the subject's human body.

[0067] System Example

[0068] According to an embodiment of the present invention, a monitoring system for carotid artery peripheral blood vessels is provided. Figure 7 A schematic diagram of a carotid artery peripheral vascular monitoring system provided in one or more embodiments of this specification is shown as follows: Figure 7 As shown, the carotid artery peripheral blood vessel monitoring system according to an embodiment of the present invention specifically includes:

[0069] The blood vessel positioning module 70 is used to locate the carotid artery using the probe of the transcranial Doppler device, fix the probe in the corresponding position, and collect blood flow signals. The probe includes two array elements. When the two array elements are combined, they are in pulse wave (PW) mode, and when they are separated, they are in continuous wave (CW) mode.

[0070] Power optimization module 72: used to optimize the operating power and transmission power parameters of the transcranial Doppler device after collecting a stable blood flow signal;

[0071] The monitoring and adjustment module 74 is used to monitor the quality of the blood flow signal in real time. If the quality of the blood flow signal is lower than a preset threshold, the power parameters are optimized again through the power optimization module.

[0072] The embodiment of the present invention is a system embodiment corresponding to the above-mentioned method embodiment. The specific operations of each module can be understood by referring to the description of the method embodiment, which will not be repeated here.

[0073] Device Example 1

[0074] An embodiment of the present invention provides an electronic device, such as Figure 8 As shown, it includes: a memory 80, a processor 82, and a computer program stored in the memory 80 and executable on the processor 82. When the computer program is executed by the processor 82, the following method steps are implemented:

[0075] S1. Locate the carotid artery using a transcranial Doppler probe, secure the probe in place, and collect blood flow signals. The probe comprises two array elements, which operate in pulsed wave (PW) mode when combined and in continuous wave (CW) mode when separated.

[0076] S2. After acquiring a stable blood flow signal, optimize the operating power and transmit power parameters of the transcranial Doppler device;

[0077] S3. Monitor the blood flow signal quality in real time. If the blood flow signal quality is lower than the preset threshold, re-implement S2 to optimize the power parameters.

[0078] Device Example 2

[0079] An embodiment of the present invention provides a computer-readable storage medium having stored thereon a program for implementing information transmission. When the program is executed by the processor 82, the following method steps are implemented:

[0080] S1. Locate the carotid artery using a transcranial Doppler probe, secure the probe in place, and collect blood flow signals. The probe comprises two array elements, which operate in pulsed wave (PW) mode when combined and in continuous wave (CW) mode when separated.

[0081] S2. After acquiring a stable blood flow signal, optimize the operating power and transmit power parameters of the transcranial Doppler device;

[0082] S3. Monitor the blood flow signal quality in real time. If the blood flow signal quality is lower than the preset threshold, re-implement S2 to optimize the power parameters.

[0083] The computer-readable storage medium in this embodiment includes, but is not limited to, ROM, RAM, magnetic disk, or optical disk.

[0084] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the above embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the above embodiments, or replace some or all of the technical features therein with equivalents. However, these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims

1. A method for monitoring carotid artery peripheral blood vessels, characterized in that: include: S1. Locate the carotid artery using a transcranial Doppler probe, secure the probe in place, and collect blood flow signals. The probe comprises two array elements, which operate in pulsed wave (PW) mode when combined and in continuous wave (CW) mode when separated. S2. After acquiring a stable blood flow signal, optimize the operating power and transmit power parameters of the transcranial Doppler device; S3. Monitor the blood flow signal quality in real time. If the blood flow signal quality is lower than the preset threshold, re-implement S2 to optimize the power parameters.

2. The method according to claim 1, characterized in that The probe has a diameter of 0.1 cm to 3 cm, a fixed tilt angle of 30 degrees to 60 degrees, and a focus located outside the carotid artery.

3. The method according to claim 2, characterized in that Use the transcranial Doppler probe to locate the carotid artery, fix the probe in the corresponding position, and collect blood flow signals. The specific method is as follows: The transcranial Doppler device uses CW mode and appropriate power for vascular positioning; After the blood flow signal is found, the probe is moved in a small range near the blood flow signal to obtain the best position for the probe, and the probe is fixed to continuously obtain the blood flow signal.

4. The method according to claim 1, wherein After collecting a stable blood flow signal, the specific method for optimizing the operating power and transmission power of the transcranial Doppler device is as follows: Switch the transcranial Doppler device to PW mode and use a larger volume to ensure that blood flow signals are obtained and that distance accumulation is performed within a range of 1 cm to 2 cm in the carotid artery depth. Determine the blood flow direction of the carotid artery, filter out negative blood flow through a complex frequency filter, and use the M-wave signal to optimize the optimal depth; When the probe's transmission mode frequently switches between PW and CW modes, an adaptive noise estimation algorithm is used to estimate the background noise of the blood flow signal. The algorithm automatically adjusts and calculates the corresponding background noise according to different modes. Optimize the scale and baseline of the sampling rate, optimize the sampling volume and emission voltage, optimize the spectrum signal-to-noise ratio, and reduce the emission power.

5. The method according to claim 4, characterized in that The optimized sampling volume is specifically: The blood flow distribution in the scanning depth direction is obtained through the M wave, and the optimal sampling volume is obtained after deconvolution of the blood flow distribution; the blood flow distribution is the result of the convolution of the sampling volume and the blood vessel diameter.

6. The method according to claim 1, characterized in that The specific method of using the adaptive noise estimation algorithm to estimate the background noise of the blood flow signal when switching between PW and CW is as follows: First, all data are divided into two categories. If the spectrum contains only noise and the noise is divided into two categories, the distance between the class centers is used to determine whether to merge them. If the variance of the noise class is large, the noise class is further decomposed into two categories. The adaptive noise estimation algorithm is used to perform two-category decomposition of noise classes 3-4 times.

7. The method according to claim 5, characterized in that The method further comprises: The AD sampling circuit of the transcranial Doppler device is controlled to only collect signals within the sampling volume, further reducing system power consumption.

8. A carotid artery peripheral blood vessel monitoring system, characterized in that: include: Vascular positioning module: used to locate the carotid artery using the probe of the transcranial Doppler device, fix the probe in the corresponding position, and collect blood flow signals; the probe includes two array elements, which operate in pulse wave (PW) mode when combined and in continuous wave (CW) mode when separated; Power optimization module: used to optimize the operating power and transmission power parameters of the transcranial Doppler device after collecting a stable blood flow signal; Monitoring and adjustment module: used to monitor the quality of blood flow signals in real time. If the quality of blood flow signals is lower than the preset threshold, the power parameters are optimized again through the power optimization module.

9. An electronic device, characterized in that: include: processor; as well as, A memory arranged to store computer-executable instructions, which, when executed, cause the processor to implement the steps of the method for monitoring carotid peripheral blood vessels according to any one of claims 1 to 7.

10. A storage medium, characterized in that: Used to store computer-executable instructions, which, when executed, implement the steps of the method for monitoring the carotid peripheral blood vessels according to any one of claims 1 to 7.

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