Ultrasonic pulse wave imaging method, device and equipment

Abstract

The invention relates to the technical field of ultrasonic imaging, and provides an ultrasonic pulse wave imaging method, device and equipment, and the method comprises the steps: calling an ultrasonic probe to carry out B-mode scanning, and determining the sampling position of a target blood vessel; aiming at the sampling position, calling the ultrasonic probe to carry out M-mode single-line scanning, determining first diameter dynamic change information of the blood vessel wall of the target blood vessel, and determining a first pulse wave conduction velocity based on the first diameter dynamic change information; aiming at the sampling position, calling the ultrasonic probe to carry out M-mode double-line scanning, determining second diameter dynamic change information of the blood vessel wall of the target blood vessel, and determining a second pulse wave conduction velocity based on the second diameter dynamic change information; and comprehensively displaying the first pulse wave conduction velocity and the second pulse wave conduction velocity. According to the technical scheme provided by one or more embodiments, the local pulse wave conduction velocity of the blood vessel can be effectively obtained.

Description

Technical Field

[0001] The present disclosure relates to the technical field of ultrasonic imaging, and in particular to an ultrasonic pulse wave imaging method, device and equipment. Background Art

[0002] The main pathological basis of cardiovascular diseases and related diseases is atherosclerosis. The early development of atherosclerosis is the change of arterial elastic function, so vascular elasticity index is one of the important predictors of cardiovascular disease. Among them, ultrasound measurement index represented by pulse wave velocity (PWV) can accurately reflect arterial elasticity. It has been widely used in clinical practice and is the gold standard for clinical evaluation of arterial elasticity. Early diagnosis of atherosclerosis is of great significance for the prevention and treatment of cardiovascular diseases.

[0003] PWV refers to the pressure wave generated by the heart contraction and ejection of blood during the cardiac cycle. The pressure wave drives the blood flow and is transmitted forward along the blood vessel wall. This wave transmitted forward along the blood vessel wall is the pulse wave. Specifically, it refers to the speed at which the pulse wave propagates from a specific position of the artery along the vessel wall to another specific position. It is usually calculated by measuring the surface distance of the arterial segment and the pulse wave transmission time.

[0004] Traditional methods of measuring PWV, such as the classic two-point measurement (including carotid artery and femoral artery, carotid artery and radial artery, and brachial artery and ankle artery, etc.), can only obtain the global and average pulse wave conduction velocity. The reason is that the hardness of human blood vessels is not uniform, and the degree of elasticity of blood vessels varies significantly after lesions occur. The PWV measured by this traditional measurement method can only reflect the average velocity between two blood vessels, and cannot truly reflect the hardness of local blood vessels in some local vascular lesions (such as atherosclerotic plaques, abdominal aortic aneurysms, etc.). Summary of the invention

[0005] In view of this, one or more embodiments of the present disclosure provide an ultrasonic pulse wave imaging method, device and apparatus, which can effectively obtain the local pulse wave conduction velocity of the blood vessel.

[0006] In a first aspect, the present disclosure provides an ultrasonic pulse wave imaging method, the method comprising: calling an ultrasonic probe to perform B-mode scanning to determine a sampling position of a target blood vessel; for the sampling position, calling the ultrasonic probe to perform M-mode single-line scanning to determine first diameter dynamic change information of a blood vessel wall of the target blood vessel, and determining a first pulse wave conduction velocity based on the first diameter dynamic change information; for the sampling position, calling the ultrasonic probe to perform M-mode double-line scanning to determine second diameter dynamic change information of the blood vessel wall of the target blood vessel, and determining a second pulse wave conduction velocity based on the second diameter dynamic change information; and comprehensively displaying the first pulse wave conduction velocity and the second pulse wave conduction velocity.

[0007] In a second aspect, the present disclosure provides an ultrasonic pulse wave imaging device, comprising: a first scanning unit, used to call an ultrasonic probe to perform B-mode scanning to determine a sampling position of a target blood vessel; a second scanning unit, used to call the ultrasonic probe to perform M-mode single-line scanning for the sampling position to determine first diameter dynamic change information of a blood vessel wall of the target blood vessel, and determine a first pulse wave conduction velocity based on the first diameter dynamic change information; a third scanning unit, used to call the ultrasonic probe to perform M-mode double-line scanning for the sampling position to determine second diameter dynamic change information of the blood vessel wall of the target blood vessel, and determine a second pulse wave conduction velocity based on the second diameter dynamic change information; and a display unit, used to comprehensively display the first pulse wave conduction velocity and the second pulse wave conduction velocity.

[0008] In a third aspect, the present disclosure provides an ultrasound device, comprising an ultrasound probe, a display, a memory and a processor; wherein the ultrasound probe is used to transmit and receive ultrasound signals; the display is used to display ultrasound images; the processor is connected to the probe, the display and the memory, and is used to control the ultrasound probe and the display, and execute a computer program stored in the memory; the memory is used to store the computer program, and when the computer program is executed by the processor, the ultrasound pulse wave imaging method of the first aspect is implemented.

[0009] In a fourth aspect, the present invention provides a computer-readable storage medium having computer instructions stored thereon, the computer instructions being used to enable a computer to execute the ultrasonic pulse wave imaging method of the first aspect.

[0010] In a fifth aspect, the present invention provides a computer program product, comprising computer instructions, wherein the computer instructions are used to enable a computer to execute the ultrasonic pulse wave imaging method of the first aspect.

[0011] The technical solution provided by one or more embodiments of the present disclosure can accurately determine the tissue structure of the target blood vessel by adopting the B mode, which is helpful for users to quickly determine some local sampling positions. Using the M mode single-line scan, the dynamic change information of the first diameter of the vascular wall of the target blood vessel can be determined, and the first pulse wave conduction velocity can be calculated. Using the M mode double-line scan, the dynamic change information of the second diameter of the vascular wall of the target blood vessel can be determined, and the second pulse wave conduction velocity can be calculated. The pulse wave conduction velocities calculated by the two different modes can complement each other, making the comprehensive display result more reliable and accurate. BRIEF DESCRIPTION OF THE DRAWINGS

[0012] The features and advantages of the embodiments of the present disclosure may be more clearly understood by referring to the accompanying drawings, which are schematic and should not be construed as limiting the present disclosure in any way. In the accompanying drawings:

[0013] Figure 1 A schematic diagram showing the steps of an ultrasonic pulse wave imaging method in one embodiment of the present disclosure is shown;

[0014] Figure 2 A schematic diagram showing the dynamic changes in the diameter of an arterial blood vessel in one embodiment of the present disclosure is shown;

[0015] Figure 3 The figure shows a schematic flow diagram of an ultrasonic pulse wave imaging method in one embodiment of the present disclosure;

[0016] Figure 4 A schematic diagram of functional modules of an ultrasonic pulse wave imaging device in one embodiment of the present disclosure is shown;

[0017] Figure 5 A schematic structural diagram of an ultrasonic device in one embodiment of the present disclosure is shown. DETAILED DESCRIPTION

[0018] In order to make the purpose, technical solutions and advantages of the embodiments of the present disclosure clearer, the technical solutions in the embodiments of the present disclosure will be clearly and completely described below in conjunction with the drawings in the embodiments of the present disclosure. Obviously, the described embodiments are part of the embodiments of the present disclosure, not all of the embodiments. Based on the embodiments of the present disclosure, all other embodiments obtained by those skilled in the art without creative work are within the scope of protection of the present disclosure.

[0019] In the related technology, the traditional pulse wave velocity measurement method has disadvantages such as unclear arterial course and multiple branch influences. It is necessary to estimate relevant parameters by measuring the surface distance, etc. The measurement error is large and only the global and average PWV can be obtained.

[0020] Among the related technologies, the first type of vascular echo tracking technology can directly obtain the local vascular wall hardness by calculating the changes in local blood pressure and blood volume, avoiding the influence of whole body measurement of vascular hardness. Its measurement principle is to track the movement of the vascular wall, record the movement trajectory of the front and back walls of the blood vessel in real time, calculate the change of the inner diameter of the blood vessel, and display it in the form of a curve, thereby calculating a number of physiological parameters such as pulse wave conduction velocity that reflect the changes in arterial elasticity.

[0021] However, this type of ultrasonic measurement technology is based on the hardness index instead of direct measurement. At the same time, obtaining these parameters requires the real-time blood pressure information of the examinee to be input. In patients with cardiovascular disease, the patient's immediate blood pressure can be affected by many factors, so the accuracy and repeatability of this method are poor.

[0022] In the related art, the second type of pulse wave velocity measurement method can be detected using ultra-high-speed imaging and tissue Doppler imaging algorithms, and the PWV at the start and end of the systolic period can be directly measured by recording the movement of the anterior wall of the carotid artery.

[0023] However, this type of ultrasonic measurement method uses ultra-high-speed imaging technology to perform Doppler estimation on the displacement of the blood vessel wall. The accuracy of blood vessel wall selection is poor and the hardware cost of its plane wave transmission is high. The defect in specific operation is that the frequency cannot be adjusted according to the subject. Subjects with slower heart rates often cannot detect results because they cannot capture a complete cardiac cycle. Since the instrument automatically identifies the arterial wall and the systolic and diastolic phases of the cardiac cycle, this link cannot be adjusted manually. Currently, only the PWV of the carotid artery can be measured. For large blood vessels such as the femoral artery and brachial artery, the arterial wall cannot be automatically identified, so it cannot be measured, which greatly limits its scope of application. The final calculation result of PWV is calculated based on a cardiac cycle captured by the system. Calculating PWV based on only one cardiac cycle will affect its accuracy.

[0024] Among the related technologies, the third method is to use ultrasound elastic imaging technology, that is, a speckle tracking method based on cross-correlation analysis, to estimate the movement of the blood vessel wall. By improving the frame rate and time resolution of ultrasound imaging, the original ultrasound RF signals at different positions are collected, and then the motion curves of the single front and back walls of the blood vessels are described. The local pulse wave velocity is directly measured through its spatiotemporal distribution, that is, the delay between different measurement positions and curves.

[0025] However, this type of ultrasonic measurement method performs speckle tracking on the displacement of the blood vessel wall, which requires a high frame rate of ultrasonic images to be collected. At the same time, due to the limitation of the central frequency of the ultrasonic probe, there is a certain error in the selection of speckles located on the blood vessel wall, and there is also the disadvantage of inaccurate ultrasonic data acquisition time.

[0026] In view of this, an ultrasonic pulse wave imaging method provided in one embodiment of the present disclosure can use the common ultrasonic B+M mode (non-ultrafast ultrasound) to obtain local rather than global, multi-cardiac cycle, combined indirect measurement and direct measurement, and user-adjustable vascular pulse wave conduction velocity. Figure 1 An ultrasonic pulse wave imaging method provided in one embodiment of the present disclosure may include the following steps.

[0027] S1: Call the ultrasound probe to perform B-mode scanning to determine the sampling position of the target blood vessel.

[0028] In this embodiment, ultrasound B-mode (Brightness Mode) can display the echo signal in the form of light spots, i.e., grayscale. The intensity of the light spots can reflect the intensity of the echo interface reflection and attenuation of ultrasound. These light spots, light rays, and light surfaces constitute a two-dimensional tomographic image or cross-sectional image of the detected part, i.e., an acoustic image. B-mode ultrasound can perform real-time imaging, can provide two-dimensional dynamic real-time imaging, and can intuitively display two-dimensional cross-sectional images of organs and diseased tissues.

[0029] In this embodiment, by using the B mode, the tissue structure of the target blood vessel can be accurately determined, which is helpful for the user to quickly determine some local sampling positions. These local sampling positions are usually areas of interest to the user. The selection criteria for the sampling positions can be: the front and back walls of the blood vessel can be clearly displayed, and the front and back walls are displayed in an ultrasound image area that is approximately parallel.

[0030] In this embodiment, the target blood vessel may include but is not limited to large blood vessels such as the carotid artery, the femoral artery, and the brachial artery.

[0031] S2: For the sampling position, calling the ultrasound probe to perform M-mode single-line scanning to determine the first diameter dynamic change information of the vascular wall of the target blood vessel, and determining the first pulse wave conduction velocity based on the first diameter dynamic change information.

[0032] In this embodiment, the ultrasound M mode (Motion Mode) can add a slow scanning sawtooth wave to the sonogram, so that the echo signal moves and scans from left to right. M mode ultrasound uses the movement of the echo light spot to observe the depth and activity of the reflector and give the corresponding time. M mode ultrasound images are mostly one-dimensional images, which can reflect the motion curve of the heart and blood vessel structure.

[0033] In this embodiment, M-mode single-line scanning uses a single sound beam to scan the sampling position of the target blood vessel, and the movement trajectory of the local blood vessel can be displayed in the form of a curve formed by the change of the light point group over time. In this mode, the ultrasound probe is relatively fixed at a certain position, and the blood vessel moves back and forth or up and down under the part where the scanning line passes to form an image. For example, please refer to Figure 2 , a change in the diameter of a blood vessel artery can be as shown by the curve in the figure.

[0034] In some embodiments, calling the ultrasound probe to perform an M-mode single-line scan to determine the first diameter dynamic change information of the vascular wall of the target blood vessel includes: within one cardiac cycle, calling the ultrasound probe to cyclically perform the B-mode scan and the M-mode single-line scan to determine the first diameter dynamic change information; wherein the transmission signal of the ultrasound probe used for the M-mode single-line scan is a single-ray ultrasonic signal; and between two adjacent ultrasonic signals transmitted by the M-mode single-line scan, there is at least one ultrasonic signal transmitted by the B-mode scan.

[0035] In the M single-line mode, at least one B-mode transmission line and corresponding echo signal must be present in the adjacent pulse repetition times of the ultrasound echo line. The main value of M mode lies in its high temporal resolution, which can capture fast-moving vascular structures. By ensuring that there is at least one B-mode transmission line, a continuous and clear temporal trajectory of the movement of vascular structures during the cardiac cycle can be obtained in M ​​mode, thereby improving the temporal resolution. In M mode, if there is no B-mode transmission line in the pulse repetition time, data discontinuity may result, thus affecting the accurate assessment of the movement of vascular structures. Retaining at least one B-mode transmission line can ensure the integrity and continuity of the data. B mode provides a two-dimensional image that can help users more accurately locate and identify vascular structures in M ​​mode. Without the assistance of B mode, relying solely on M mode may cause measurement errors due to the rapid movement of vascular structures. The presence of B mode can help correct this error, especially when evaluating cardiac systolic and diastolic function. By combining B mode and M mode, users can more confidently assess the movement of blood vessels, which can provide more comprehensive assessment information. The transmission line of B mode can also enhance the image quality in M ​​mode, especially in the display of the boundaries of vascular structures, which is crucial for the accurate assessment of vascular function.

[0036] In some embodiments, determining a first pulse wave velocity based on the first diameter dynamic change information includes: acquiring blood pressure information of the target object, the blood pressure information including systolic pressure information and diastolic pressure information; determining the first pulse wave velocity based on the maximum diameter of the vascular artery and the minimum diameter of the vascular artery contained in the first diameter dynamic change information, as well as the systolic pressure information and the diastolic pressure information.

[0037] In some embodiments, the first pulse wave conduction velocity is determined based on the maximum diameter of the vascular artery and the minimum diameter of the vascular artery, as well as the systolic pressure information and the diastolic pressure information contained in the first diameter dynamic change information, including: determining a vascular hardening index based on the maximum diameter of the vascular artery, the minimum diameter of the vascular artery, the systolic pressure information, and the diastolic pressure information; and determining the first pulse wave conduction velocity based on the vascular hardening index, the systolic pressure information, and the pre-acquired blood density of the target object.

[0038] By using the ultrasound probe to perform M-mode single-line scanning, the dynamic change information of the diameter of the front and back walls of the blood vessels corresponding to the same position at different time points can be obtained. At this time, the blood pressure information of the target object (the person being tested) can be obtained in advance, and the conduction velocity of the vascular pulse wave can be derived using a preset formula, which is an indirect measurement method.

[0039] In an actual application example, after the user inputs the blood pressure value parameter, the vascular hardening index can be determined first according to the following formula:

[0040]

[0041] Among them, β is the degree of vascular sclerosis, P s is systolic blood pressure, P d is diastolic blood pressure, D s D is the maximum diameter of the artery. d It is the smallest diameter of a blood vessel artery.

[0042] Then, the vascular pulse wave velocity PWV can be calculated by the following formula: β :

[0043]

[0044] Where ρ is the blood density.

[0045] S3: For the sampling position, calling the ultrasound probe to perform M-mode dual-line scanning to determine the second diameter dynamic change information of the vascular wall of the target blood vessel, and determining the second pulse wave conduction velocity based on the second diameter dynamic change information.

[0046] In this embodiment, M-mode dual-line scanning is developed based on M-mode single-line scanning, and can display two parallel M-mode tracks at the same time. This mode is achieved by placing two parallel sampling lines on a two-dimensional image, which can more comprehensively evaluate the movement of blood vessels. M-mode dual-line scanning can provide more accurate vascular information.

[0047] In some embodiments, within two cardiac cycles, the ultrasound probe is called to cyclically perform the B-mode scanning and the M-mode dual-line scanning to determine the dynamic change information of the second diameter; wherein the transmission signal of the ultrasound probe used for the M-mode dual-line scanning is a dual-ray ultrasonic signal; and between two adjacent ultrasonic signals transmitted by the M-mode dual-line scanning, there is at least one ultrasonic signal transmitted by the B-mode scanning.

[0048] In some embodiments, determining the second pulse wave conduction velocity based on the second diameter dynamic change information includes: determining the local conduction distance of the vascular pulse wave according to the lateral spacing between adjacent ultrasonic array elements used for the M-mode dual-line scanning in the ultrasonic probe; performing cross-correlation analysis based on the second diameter dynamic change information to determine the local conduction time of the vascular pulse wave; and determining the second pulse wave conduction velocity based on the local conduction distance and the local conduction time.

[0049] The dual-line scanning in M ​​mode is the simultaneous transmission and reception of several adjacent ultrasonic array elements, and the lateral spacing should be less than half of the pulse wave conduction distance during this period to ensure the tracking range and accuracy of the pulse wave. The lateral spacing between the two lines is used as the local conduction distance of the vascular pulse wave. Preferably, the lateral spacing can be adjusted between 2-15mm.

[0050] The corresponding pulse wave transmission delay time can obtain the dynamic change of the vessel wall diameter over time and outline the radial size of the vessel. Subsequently, the local transmission time of the vascular pulse wave can be derived by applying cross-correlation analysis to the dynamic change of the vessel diameter extracted from the two echo lines. The cross-correlation delay estimation method calculates the time delay between the two signals by comparing their similarity.

[0051] In some embodiments, the ultrasonic emission mode of the ultrasonic probe performing the M-mode single-line scanning includes a deflection mode and a non-deflection mode; the ultrasonic emission mode of the ultrasonic probe performing the M-mode double-line scanning includes a deflection mode and a non-deflection mode.

[0052] The deflection mode (phased array technology) can achieve the deflection and focusing of the sound beam by electronically controlling the phase difference of each array element, and can perform fan-shaped or cone-shaped scanning without mechanical movement. This flexibility makes the phased array probe shine in ultrasound examination, which can clearly display the complex structure of blood vessels, blood flow dynamics and vascular function evaluation. Phased array technology can provide a higher defect detection rate, intuitive imaging and fast detection speed.

[0053] The ultrasonic probe structure of the non-deflection mode (traditional ultrasonic probe) is relatively simple, usually using a single probe or a mechanical probe, and is suitable for ultrasonic diagnostic instruments with A-type, M-type, mechanical fan scanning and pulse Doppler working modes. Due to its simple structure, the ultrasonic probe of the non-deflection mode is low in cost and suitable for occasions with limited budget.

[0054] S4: Comprehensively displaying the first pulse wave velocity and the second pulse wave velocity.

[0055] In this embodiment, the pulse wave velocities of the above two methods are comprehensively displayed in real time in the user operation interface in the form of numerical weighting. For example, the two pulse wave velocities can be displayed simultaneously, and their respective weight references can be given; only the first pulse wave velocity and the third pulse wave velocity weighted by the second pulse wave velocity can be displayed; or the first pulse wave velocity, the second pulse wave velocity and the third pulse wave velocity can be displayed simultaneously.

[0056] In some embodiments, with respect to the sampling position, the ultrasound probe is called to perform the M-mode single-line scan to determine first change information of the anterior wall of the target blood vessel and second change information of the posterior wall of the target blood vessel; based on the first change information and the second change information, a first dynamic change curve of the difference between the anterior wall and the posterior wall of the target blood vessel is determined; a linear fit is performed on the first dynamic change curve to obtain first fitting data; and based on the first fitting data, the first pulse wave conduction velocity is determined.

[0057] In some embodiments, with respect to the sampling position, the ultrasound probe is called to perform the M-mode dual-line scan to determine third change information of the anterior wall of the target blood vessel and fourth change information of the posterior wall of the target blood vessel; a second dynamic change curve of the difference between the anterior wall and the posterior wall of the target blood vessel is determined based on the third change information and the fourth change information; the second dynamic change curve is linearly fitted to obtain second fitting data; and the second pulse wave conduction velocity is determined based on the second fitting data.

[0058] Even if there is already information about the curve of the change in vascular diameter, it is still valuable and meaningful to perform linear fitting. The main reasons include: data in the real world is often complex, while linear models are relatively simple and easy to understand and process. Through linear fitting, complex curve changes can be simplified into a straight line, making it easier to understand and analyze the data. Linear fitting can help identify the main trends in the data. Even if the change in vascular diameter is not completely linear, linear fitting can provide an approximation of the trend, which is very useful for quickly identifying the direction of change (increase or decrease) and the rate of change (fast or slow). Linear fitting provides a way to quantify the change. By calculating the slope and intercept, the rate of change and initial state of vascular diameter over time can be quantified, which is very important for statistical analysis and comparison of changes under different conditions. Linear models can be used to predict future changes. If the linear relationship of vascular diameter over time is known, this model can be used to predict future changes in vascular diameter. In addition, linear models can also be used to interpolate between known data points to estimate the vascular diameter at unknown time points. By comparing the actual data points with the best fitting straight line, abnormal points that deviate from the linear trend can be identified. These abnormal points may indicate special physiological states or pathological changes that require further analysis and attention.

[0059] The technical solution provided by one or more embodiments of the present disclosure can accurately determine the tissue structure of the target blood vessel by adopting the B mode, which is helpful for users to quickly determine some local sampling positions. Using the M mode single-line scan, the dynamic change information of the first diameter of the vascular wall of the target blood vessel can be determined, and the first pulse wave conduction velocity can be calculated. Using the M mode double-line scan, the dynamic change information of the second diameter of the vascular wall of the target blood vessel can be determined, and the second pulse wave conduction velocity can be calculated. The pulse wave conduction velocities calculated by the two different modes can complement each other, making the comprehensive display result more reliable and accurate.

[0060] See also Figure 3 The technical solution provided by one or more embodiments of the present disclosure can quickly screen the area of ​​interest to the user, that is, the sampling position of the target blood vessel, based on the B-mode scan. By calling the ultrasound probe for M-mode single-line scanning, the dynamic change information of the diameter of the front and back walls of the blood vessel corresponding to different time points at the same position can be obtained, and the conduction velocity of the blood vessel pulse wave can be derived in combination with a preset formula, which is an indirect measurement method. By calling the ultrasound probe for M-mode double-line scanning, the dynamic change information of the inner diameter of the corresponding blood vessel wall can be determined at different times in two positions. By collecting two-line ultrasonic echo data, the conduction distance and corresponding conduction time of the pulse wave can be measured, thereby realizing direct measurement of the local blood vessel pulse wave velocity. Finally, the pulse wave conduction velocity measured by the two methods can be comprehensively displayed in the form of numerical weighting on the user operation interface, overcoming the error of a single measurement method.

[0061] The technical solution provided by one or more embodiments of the present disclosure can obtain local rather than global, multi-cardiac cycle, user-adjustable vascular pulse wave conduction velocity that combines indirect measurement and direct measurement, and the measurement results are more flexible, accurate and reliable.

[0062] See also Figure 4 The present disclosure also provides an ultrasonic pulse wave imaging device, the device comprising:

[0063] The first scanning unit 100 is used to call the ultrasound probe to perform B-mode scanning to determine the sampling position of the target blood vessel;

[0064] The second scanning unit 200 is used to call the ultrasound probe to perform M-mode single-line scanning for the sampling position, determine the first diameter dynamic change information of the vascular wall of the target blood vessel, and determine the first pulse wave conduction velocity based on the first diameter dynamic change information;

[0065] The third scanning unit 300 is used to call the ultrasound probe to perform M-mode dual-line scanning for the sampling position to determine the second diameter dynamic change information of the vascular wall of the target blood vessel, and determine the second pulse wave velocity based on the second diameter dynamic change information;

[0066] The display unit 400 is used to comprehensively display the first pulse wave velocity and the second pulse wave velocity.

[0067] In one embodiment, the second scanning unit 200 is specifically used to call the ultrasound probe to cyclically perform the B-mode scanning and the M-mode single-line scanning within one cardiac cycle to determine the dynamic change information of the first diameter; wherein the transmission signal of the ultrasound probe used for the M-mode single-line scanning is a single-ray ultrasonic signal; and between two adjacent ultrasonic signals transmitted by the M-mode single-line scanning, there is at least one ultrasonic signal transmitted by the B-mode scanning.

[0068] In one embodiment, the second scanning unit 200 is specifically used to obtain blood pressure information of the target object, wherein the blood pressure information includes systolic pressure information and diastolic pressure information; based on the maximum diameter of the vascular artery and the minimum diameter of the vascular artery contained in the first diameter dynamic change information, as well as the systolic pressure information and the diastolic pressure information, the first pulse wave conduction velocity is determined.

[0069] In one embodiment, the second scanning unit 200 is further used to determine a vascular hardness index based on the maximum diameter of the vascular artery, the minimum diameter of the vascular artery, the systolic pressure information and the diastolic pressure information; and to determine the first pulse wave conduction velocity based on the vascular hardness index, the systolic pressure information and the pre-acquired blood density of the target object.

[0070] In one embodiment, the third scanning unit 300 is specifically used to call the ultrasound probe to cyclically perform the B-mode scanning and the M-mode dual-line scanning within two cardiac cycles to determine the dynamic change information of the second diameter; wherein the transmission signal of the ultrasound probe used for the M-mode dual-line scanning is a dual-ray ultrasonic signal; and between two adjacent ultrasonic signals transmitted by the M-mode dual-line scanning, there is at least one ultrasonic signal transmitted by the B-mode scanning.

[0071] In one embodiment, the third scanning unit 300 is specifically used to determine the local conduction distance of the blood vessel pulse wave according to the lateral spacing between adjacent ultrasonic array elements used for the M-mode dual-line scanning in the ultrasonic probe; perform cross-correlation analysis based on the second diameter dynamic change information to determine the local conduction time of the blood vessel pulse wave; and determine the second pulse wave conduction velocity based on the local conduction distance and the local conduction time.

[0072] In one embodiment, the ultrasonic emission mode of the ultrasonic probe performing the M-mode single-line scanning includes a deflection mode and a non-deflection mode; the ultrasonic emission mode of the ultrasonic probe performing the M-mode double-line scanning includes a deflection mode and a non-deflection mode.

[0073] In one embodiment, the device also includes a first fitting unit 500, which is used to call the ultrasound probe to perform the M-mode single-line scan for the sampling position to determine the first change information of the anterior wall of the target blood vessel and the second change information of the posterior wall of the target blood vessel; determine a first dynamic change curve of the difference between the anterior wall and the posterior wall of the target blood vessel based on the first change information and the second change information; perform linear fitting on the first dynamic change curve to obtain first fitting data; and determine the first pulse wave conduction velocity based on the first fitting data.

[0074] In one embodiment, the device also includes a second fitting unit 600, which is used to call the ultrasound probe to perform the M-mode dual-line scanning for the sampling position to determine the third change information of the anterior wall of the target blood vessel and the fourth change information of the posterior wall of the target blood vessel; determine a second dynamic change curve of the difference between the anterior wall and the posterior wall of the target blood vessel based on the third change information and the fourth change information; perform linear fitting on the second dynamic change curve to obtain second fitting data; and determine the second pulse wave conduction velocity based on the second fitting data.

[0075] Each unit described in the above embodiments may be implemented by a computer chip or a product having a certain function. A typical implementation device is a computer. Specifically, the computer may be, for example, a personal computer, a laptop computer, a cellular phone, a camera phone, a smart phone, a personal digital assistant, a media player, a navigation device, an email device, a game console, a tablet computer, a wearable device, or a combination of any of these devices.

[0076] For the convenience of description, the above devices are described in terms of functions and are described separately in various units. Of course, when implementing the present application, the functions of each unit can be implemented in the same or multiple software and / or hardware.

[0077] See also Figure 5 The present disclosure also provides an ultrasound device, wherein the electronic device includes a memory and a processor. The ultrasound probe is used to transmit and receive ultrasound signals. The display is used to display ultrasound images. The processor is connected to the probe, the display unit and the memory module, respectively, and is configured to execute the above-mentioned ultrasound pulse wave imaging method. The memory is used to store a computer program, and when the computer program is executed by the processor, the above-mentioned ultrasound pulse wave imaging method is implemented.

[0078] The processor may be a central processing unit (CPU). The processor may also be other general-purpose processors, digital signal processors (DSP), application-specific integrated circuits (ASIC), field-programmable gate arrays (FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, or a combination of the above chips.

[0079] As a non-transitory computer-readable storage medium, the memory can be used to store non-transitory software programs, non-transitory computer executable programs and modules, such as program instructions / modules corresponding to the method in the embodiment of the present disclosure. The processor executes various functional applications and data processing of the processor by running the non-transitory software programs, instructions and modules stored in the memory, that is, implementing the method in the above method embodiment.

[0080] The memory may include a program storage area and a data storage area, wherein the program storage area may store an operating system, an application required for at least one function; the data storage area may store data created by the processor, etc. In addition, the memory may include a high-speed random access memory, and may also include a non-transitory memory, such as at least one disk storage device, a flash memory device, or other non-transitory solid-state storage device. In some embodiments, the memory may optionally include a memory remotely disposed relative to the processor, and these remote memories may be connected to the processor via a network. Examples of the above-mentioned network include, but are not limited to, the Internet, an intranet, a local area network, a mobile communication network, and combinations thereof.

[0081] Those skilled in the art can understand that all or part of the processes in the above-mentioned embodiments can be implemented by instructing the relevant hardware through a computer program, and the program can be stored in a computer-readable storage medium, and when the program is executed, it can include the processes of the embodiments of the above-mentioned methods. Among them, the storage medium can be a disk, an optical disk, a read-only memory (ROM), a random access memory (RAM), a flash memory, a hard disk drive (HDD) or a solid-state drive (SSD), etc.; the storage medium can also include a combination of the above-mentioned types of memory.

[0082] The present disclosure also provides a computer-readable storage medium, wherein the computer-readable storage medium is used to store a computer program, and when the computer program is executed by a processor, the above-mentioned ultrasonic pulse wave imaging method is implemented.

[0083] The above-mentioned method according to the embodiment of the present invention can be implemented in hardware, firmware, or can be implemented as a computer code that can be recorded in a storage medium, or can be implemented as a computer code that is originally stored in a remote storage medium or a non-temporary machine-readable storage medium and will be stored in a local storage medium and downloaded through a network, so that the method described herein can be stored in such software processing on a storage medium using a general-purpose computer, a dedicated processor, or programmable or dedicated hardware. Among them, the storage medium can be a magnetic disk, an optical disk, a read-only storage memory, a random access memory, a flash memory, a hard disk or a solid-state hard disk, etc.; further, the storage medium can also include a combination of the above-mentioned types of memory. It can be understood that a computer, a processor, a microprocessor controller or programmable hardware includes a storage component that can store or receive software or computer code. When the software or computer code is accessed and executed by a computer, a processor or hardware, the method shown in the above embodiment is implemented.

[0084] Part of the present invention may also be applied as a computer program product, such as a computer program instruction, which, when executed by a computer, can call or provide the method and / or technical solution according to the present invention through the operation of the computer. Those skilled in the art should understand that the existence of computer program instructions in computer-readable media includes, but is not limited to, source files, executable files, installation package files, etc., and accordingly, the way in which computer program instructions are executed by a computer includes, but is not limited to: the computer directly executes the instruction, or the computer compiles the instruction and then executes the corresponding compiled program, or the computer reads and executes the instruction, or the computer reads and installs the instruction and then executes the corresponding installed program. Here, the computer-readable medium may be any available computer-readable storage medium or communication medium accessible to the computer.

[0085] Each embodiment in this specification is described in a progressive manner, and the same or similar parts between the embodiments can be referred to each other, and each embodiment focuses on the differences from other embodiments. In particular, for the embodiments of the device, equipment, and storage medium, since they are basically similar to the method embodiments, the description is relatively simple, and the relevant parts can be referred to the partial description of the method embodiments.

[0086] The above is only an embodiment of the present application and is not intended to limit the present application. For those skilled in the art, the present application may have various changes and variations. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application should be included in the scope of the claims of the present application.

[0087] Although the embodiments of the present disclosure have been described in conjunction with the accompanying drawings, those skilled in the art may make various modifications and variations without departing from the spirit and scope of the present disclosure, and such modifications and variations are all within the scope defined by the appended claims.

Claims

1. An ultrasonic pulse wave imaging method, characterized in that: The method comprises: Call the ultrasound probe to perform B-mode scanning to determine the sampling position of the target blood vessel; For the sampling position, calling the ultrasound probe to perform M-mode single-line scanning to determine first diameter dynamic change information of the vascular wall of the target blood vessel, and determining a first pulse wave conduction velocity based on the first diameter dynamic change information; For the sampling position, calling the ultrasound probe to perform M-mode dual-line scanning to determine the second diameter dynamic change information of the vascular wall of the target blood vessel, and determining the second pulse wave conduction velocity based on the second diameter dynamic change information; The first pulse wave velocity and the second pulse wave velocity are comprehensively displayed.

2. The method according to claim 1, characterized in that The calling of the ultrasound probe to perform M-mode single-line scanning to determine the dynamic change information of the first diameter of the vascular wall of the target blood vessel includes: In one cardiac cycle, calling the ultrasound probe to cyclically perform the B-mode scanning and the M-mode single-line scanning to determine the first diameter dynamic change information; Among them, the transmission signal of the ultrasonic probe used for the M-mode single-line scanning is a single-ray ultrasonic signal; between two adjacent ultrasonic signals transmitted by the M-mode single-line scanning, there is at least one ultrasonic signal transmitted by the B-mode scanning.

3. The method according to claim 1 or 2, characterized in that: The determining of a first pulse wave velocity based on the first diameter dynamic change information includes: Acquiring blood pressure information of a target object, wherein the blood pressure information includes systolic pressure information and diastolic pressure information; The first pulse wave velocity is determined based on the maximum diameter of the vascular artery and the minimum diameter of the vascular artery included in the first diameter dynamic change information, as well as the systolic pressure information and the diastolic pressure information.

4. The method according to claim 3, characterized in that The determining of the first pulse wave velocity based on the maximum diameter of the blood vessel artery and the minimum diameter of the blood vessel artery, as well as the systolic pressure information and the diastolic pressure information included in the first diameter dynamic change information includes: Determining a vascular sclerosis index based on the maximum diameter of the vascular artery, the minimum diameter of the vascular artery, the systolic pressure information, and the diastolic pressure information; The first pulse wave velocity is determined based on the vascular hardness index, the systolic blood pressure information, and a pre-acquired blood density of the target subject.

5. The method according to claim 1, characterized in that The calling of the ultrasound probe to perform M-mode dual-line scanning to determine the second diameter dynamic change information of the vascular wall of the target blood vessel includes: In two cardiac cycles, calling the ultrasound probe to cyclically perform the B-mode scanning and the M-mode dual-line scanning to determine the second diameter dynamic change information; Among them, the transmission signal of the ultrasonic probe used for the M-mode dual-line scanning is a dual-ray ultrasonic signal; between two adjacent ultrasonic signals transmitted by the M-mode dual-line scanning, there is at least one ultrasonic signal transmitted by the B-mode scanning.

6. The method according to claim 1 or 5, characterized in that: The determining of the second pulse wave velocity based on the second diameter dynamic change information includes: Determining the local conduction distance of the blood vessel pulse wave according to the lateral spacing between adjacent ultrasound array elements used for the M-mode dual-line scanning in the ultrasound probe; Based on the second diameter dynamic change information, cross-correlation analysis is performed to determine the local conduction time of the blood vessel pulse wave; The second pulse wave velocity is determined based on the local conduction distance and the local conduction time.

7. The method according to claim 1, characterized in that The ultrasonic emission modes of the ultrasonic probe for performing the M-mode single-line scanning include a deflection mode and a non-deflection mode; the ultrasonic emission modes of the ultrasonic probe for performing the M-mode double-line scanning include a deflection mode and a non-deflection mode.

8. The method according to claim 1, characterized in that The method further comprises: For the sampling position, calling the ultrasound probe to perform the M-mode single-line scan to determine first change information of the anterior wall of the target blood vessel and second change information of the posterior wall of the target blood vessel; Determine a first dynamic change curve of the difference between the front wall and the back wall of the target blood vessel according to the first change information and the second change information; Performing linear fitting on the first dynamic change curve to obtain first fitting data; determining the first pulse wave velocity according to the first fitting data; and / or, For the sampling position, calling the ultrasound probe to perform the M-mode dual-line scanning to determine third change information of the anterior wall of the target blood vessel and fourth change information of the posterior wall of the target blood vessel; Determine a second dynamic change curve of the difference between the front wall and the back wall of the target blood vessel according to the third change information and the fourth change information; Performing linear fitting on the second dynamic change curve to obtain second fitting data; The second pulse wave velocity is determined based on the second fitting data.

9. An ultrasonic pulse wave imaging device, characterized in that: The device comprises: A first scanning unit is used to call an ultrasound probe to perform B-mode scanning to determine a sampling position of a target blood vessel; a second scanning unit, configured to call the ultrasound probe to perform an M-mode single-line scan for the sampling position, determine first diameter dynamic change information of the vascular wall of the target blood vessel, and determine a first pulse wave velocity based on the first diameter dynamic change information; a third scanning unit, configured to call the ultrasound probe to perform an M-mode dual-line scan at the sampling position to determine second diameter dynamic change information of the vascular wall of the target blood vessel, and determine a second pulse wave velocity based on the second diameter dynamic change information; The display unit is used to comprehensively display the first pulse wave velocity and the second pulse wave velocity.

10. An ultrasonic device, characterized in that: The ultrasound device includes an ultrasound probe, a display, a memory and a processor; wherein, The ultrasonic probe is used to transmit and receive ultrasonic signals; The display is used to display ultrasound images; The processor is connected to the probe, the display and the memory, and is used to control the ultrasound probe and the display, and execute the computer program stored in the memory; The memory is used to store the computer program, and when the computer program is executed by the processor, the ultrasonic pulse wave imaging method according to any one of claims 1 to 8 is implemented.

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