CN115381489A - Method and device for measuring ultrasonic blood flow parameters and ocular vascular indexes - Google Patents

Abstract

A method and device for measuring ultrasonic blood flow parameters and ocular vascular index, the method comprising: acquiring a first position of interest and a second position of interest on an ultrasonic image of a target blood vessel; determining the first position of interest and the second position of interest A connection line between positions of interest, wherein the connection line includes a plurality of divided intervals; for each interval, the vector blood flow velocity at the two ends of the interval and the interval length of the interval are obtained, and based on the vector blood flow velocity and the interval The length calculates the blood pressure difference between the two ends of the interval; based on the size of the blood pressure difference between the two ends of each interval, the corresponding color is displayed on different intervals of the connection line to present the first interest position and the second Trend of blood pressure difference between locations of interest. The application enables accurate calculation of local differential pressure.

Description

Method and device for measuring ultrasonic blood flow parameters and ocular vascular index

technical field

The present application relates to the technical field of ultrasonic scanning, and more particularly relates to a method and device for measuring blood flow parameters and ocular vascular index based on ultrasonic waves.

Background technique

When the heart valves (including aortic valve, tricuspid valve, mitral valve, pulmonary valve, etc.) are abnormal, there will be an abnormal drop in local blood pressure after passing through the valve; arterial stenosis will cause a significant drop in local blood pressure when the blood flow passes through the stenosis; Problems with the baroreceptors of the carotid sinus and aortic arch may cause high blood pressure; when the venous valve is abnormally regurgitated, the local blood pressure changes abnormally, causing blood to flow back and may cause thrombus; excessively elevated intraocular pressure is a relatively serious eye disease. Studies have shown that there is a certain relationship between retinal arteriosclerosis and blood pressure and intraocular pressure.

It can be seen that the measurement of local blood pressure changes has certain clinical value for the diagnosis and research of many diseases. A needle can measure the pressure inside the blood vessel, but this is invasive. Common non-invasive methods mainly include intravascular pressure difference measurement methods based on magnetic resonance imaging (MRI) or continuous Doppler (CW). However, MRI examination takes a long time and costs high, and CW lacks specific measurement location information. Therefore, in order to popularize accurate measurement of regional blood pressure in clinical examination, more advanced ultrasonic measurement methods and techniques are needed.

Contents of the invention

According to one aspect of the present application, a method for measuring ultrasonic blood flow parameters is provided, the method comprising: acquiring a first position of interest and the second position of interest on an ultrasonic image of a target blood vessel; determining the first position of interest A connection line between the location of interest and the second location of interest, wherein the connection line includes a plurality of divided intervals; for each of the intervals, obtain the vector blood flow velocity at the two ends of the interval and the interval length of the interval, and calculate the blood pressure difference between the two ends of the interval based on the vector blood flow velocity and the interval length; based on the blood pressure difference between the two ends of each interval Corresponding colors are displayed on different intervals of the connecting line, so as to present the variation trend of the blood pressure difference between the first location of interest and the second location of interest.

According to another aspect of the present application, a method for measuring ultrasonic blood flow parameters is provided, the method comprising: acquiring a connection line drawn by a user on an ultrasound image of a target blood vessel, wherein the connection line includes a plurality of divided intervals; For each interval, obtain the vector blood flow velocity at the two ends of the interval and the interval length of the interval, and calculate the two end positions of the interval based on the vector blood flow velocity and the interval length Based on the blood pressure difference between the two ends of each of the intervals, corresponding colors are displayed on different intervals of the line to present the change trend of the blood pressure difference on the line .

According to still another aspect of the present application, a method for measuring ultrasonic blood flow parameters is provided, the method comprising: transmitting ultrasonic waves to the target blood vessel along at least two different scanning angles, receiving the echoes of the ultrasonic waves, and based on the Obtaining at least two groups of ultrasonic echo signals, wherein each group of ultrasonic echo signals originates from ultrasonic waves emitted at a scanning angle; obtaining a first position of interest and a second position of interest on the ultrasonic image of the target blood vessel , and the length between the first position of interest and the second position of interest; based on the at least two groups of ultrasonic echo signals, at least two velocity components at the first position of interest and the at least two velocity components at the second position of interest, and synthesize at least two velocity components at each position of interest to obtain a vector blood flow velocity at each position of interest, wherein each velocity component derived from a set of ultrasound echo signals; based on the vector blood flow velocity at the first location of interest, the vector blood flow velocity at the second location of interest, and the first location of interest and the second The length between locations of interest calculates a blood pressure difference between the first location of interest and the second location of interest.

According to yet another aspect of the present application, a method for measuring an ocular vascular index is provided, the method comprising: acquiring a blood pressure difference between a first position of interest and a second position of interest on an ultrasound image of a target vessel, wherein , the first position of interest and the second position of interest are respectively located in the common carotid artery and the internal carotid artery; the blood flow parameters of the ocular blood vessels communicating with the internal carotid artery are obtained, and the blood flow parameters include contraction Phase peak flow velocity and end-diastole flow velocity; calculate the velocity difference between the systolic peak flow velocity and the end-diastole flow velocity, and calculate and output the ratio of the blood pressure difference to the velocity difference.

According to still another aspect of the present application, an ultrasonic blood flow imaging device is provided, the ultrasonic blood flow imaging device includes a transmitting circuit, a receiving circuit, an ultrasonic probe, a processor and a display, wherein: the transmitting circuit is used to control the The ultrasonic probe transmits ultrasonic waves to the target part of the target object; the receiving circuit is used to control the ultrasonic probe to receive the echoes of the ultrasonic waves, and obtain ultrasonic echo signals from the echoes of the ultrasonic waves; the processor is used to The ultrasonic echo signal is used for ultrasonic blood flow imaging; the processor is also used for executing the above method for measuring ultrasonic blood flow parameters; and the display is used for displaying the result output by the processor.

The method and device for measuring ultrasonic blood flow parameters and ocular vascular index according to the embodiments of the present application can realize accurate calculation of local pressure difference, and is non-invasive and fast; in addition, the measurement method of ultrasonic blood flow parameters according to the embodiments of the present application is based on Multiple vector blood flow velocities in the area between two positions of interest on the target blood vessel ultrasound image generate a pressure gradient map between the two positions of interest, which can realize the intuitive presentation of the trend of pressure difference between the two positions of interest , so as to better assist doctors in diagnosis; in addition, the measurement method of ocular vascular index calculates the parameters related to ocular blood supply based on the pressure drop at the carotid sinus, which can provide doctors with ocular diseases, especially ischemic ocular Clinical research and related guidance for certain diseases.

Description of drawings

The above and other objects, features and advantages of the present application will become more apparent through a more detailed description of the embodiments of the present application in conjunction with the accompanying drawings. The accompanying drawings are used to provide a further understanding of the embodiments of the present application, and constitute a part of the specification, and are used together with the embodiments of the present application to explain the present application, and do not constitute limitations to the present application. In the drawings, the same reference numerals generally represent the same components or steps.

Fig. 1 shows a schematic flowchart of a method for measuring ultrasonic blood flow parameters according to an embodiment of the present application.

Fig. 2 shows an exemplary schematic diagram of two positions of interest and a connection line between them in the method for measuring ultrasonic blood flow parameters according to an embodiment of the present application.

Fig. 3 shows an exemplary schematic diagram of two positions of interest and a connection line between them in the method for measuring ultrasonic blood flow parameters according to an embodiment of the present application.

Fig. 4 shows an exemplary schematic diagram of the variation trend of blood pressure difference in the method for measuring ultrasonic blood flow parameters according to an embodiment of the present application.

Fig. 5 shows a schematic flowchart of a method for measuring ultrasonic blood flow parameters according to another embodiment of the present application.

Fig. 6 shows a schematic flowchart of a method for measuring ultrasonic blood flow parameters according to yet another embodiment of the present application.

Fig. 7 shows an exemplary schematic diagram of three positions of interest and the lines between them in the method for measuring ultrasonic blood flow parameters according to yet another embodiment of the present application.

Fig. 8 shows a schematic flowchart of a method for measuring ultrasonic blood flow parameters according to yet another embodiment of the present application.

Fig. 9 shows a schematic flowchart of a method for measuring an ocular vascular index according to yet another embodiment of the present application.

Fig. 10 shows an exemplary schematic diagram of two positions of interest in a method for measuring an ocular vascular index according to yet another embodiment of the present application.

Fig. 11 shows a schematic structural block diagram of an ultrasonic blood flow imaging device according to an embodiment of the present application.

Detailed ways

In order to make the objects, technical solutions, and advantages of the present application more apparent, exemplary embodiments according to the present application will be described in detail below with reference to the accompanying drawings. Apparently, the described embodiments are only some of the embodiments of the present application, rather than all the embodiments of the present application. It should be understood that the present application is not limited by the exemplary embodiments described here. Based on the embodiments of the present application described in the present application, all other embodiments obtained by those skilled in the art without creative efforts shall fall within the protection scope of the present application.

First, a method for measuring ultrasonic blood flow parameters according to an embodiment of the present application will be described with reference to FIG. 1 . Fig. 1 shows a schematic flowchart of a method 100 for measuring ultrasonic blood flow parameters according to an embodiment of the present application. As shown in FIG. 1, a method 100 for measuring blood flow parameters based on ultrasound may include the following steps:

In step S110, a first position of interest and a second position of interest on the ultrasonic image of the target blood vessel are acquired.

In the embodiment of the present application, the ultrasonic imaging of the target blood vessel can be performed first to obtain the ultrasonic image of the target blood vessel, which is displayed to the user, and the user can determine the two positions of interest ( For example, through a user interaction interface), that is, the first location of interest and the second location of interest. Therefore, according to the user's operation, the first location of interest and the second location of interest selected by the user can be obtained. In other examples, the ultrasound system can also automatically select two positions of interest in some cases. For example, the system can automatically determine the position where the blood pressure difference is to be measured if the system finds that there may be a problem somewhere in the blood vessel through detection.

Figures 2 and 3 show two examples of two locations of interest within a blood vessel, respectively. Wherein, FIG. 2 shows a schematic diagram of a bifurcated blood vessel, such as a carotid artery bifurcation. When it is desired to measure the blood pressure difference from the common carotid artery to the internal carotid artery, two positions of interest can be determined automatically or manually by the user, such as A first location of interest A and a second location of interest B shown in FIG. 2 . Figure 3 shows a schematic diagram of a blood vessel with plaque. When the system detects that there is plaque somewhere in the blood vessel, it can automatically determine the positions of interest on both sides of the plaque, as shown in Figure 3. The first position of interest A and A second location of interest, B, to measure the pressure drop after blood flow through the plaque. Certainly, the two positions of interest shown in FIG. 3 may also be determined by the user.

In step S120, a connection line between the first location of interest and the second location of interest is determined, wherein the connection line includes a plurality of divided intervals.

In the embodiment of the present application, after the first location of interest and the second location of interest are obtained, the connection between the first location of interest and the second location of interest can be determined, wherein the connection is a continuous The connecting lines connected to the first position of interest and the second position of interest respectively, and the connecting line is divided into a plurality of intervals. The connection line may be a straight line, a broken line, a curve or an irregularly shaped line, which is not specifically limited here. The connection line can be in the shape of a line or a strip, that is to say, it can have a certain thickness. In the embodiment of the present application, the purpose of dividing the line between two locations of interest into multiple intervals is to calculate the blood pressure difference for each interval, so as to obtain the change trend of the pressure difference between the two locations of interest, Thereby, the measurement of local blood pressure changes can be realized more accurately, as will be described in steps S130 to S140 below.

Exemplarily, the line between the first position of interest and the second position of interest (such as the line between the first position of interest A and the second position of interest B as shown in FIG. 2 and FIG. 3 ) , the line can be divided into multiple line segments as multiple intervals (such as the line between the first position of interest A and the second position of interest B as shown in Figure 4 is divided into equidistant or unequal multiple segments of the distance). In one example, the connection line between the first position of interest and the second position of interest can be automatically generated according to the trends of the blood vessels where the first position of interest and the second position of interest are located, so that the line is roughly in line with the Axes remain the same. Specifically, the distances from the points on the line to the front wall and the back wall of the blood vessel are approximately the same, so that the line is approximately in the middle area of the blood vessel. The blood flow roughly flows along the trend direction of the blood vessels. This method can describe the approximate blood flow path, especially for the blood vessels at the bifurcation, which can well present the blood flow trend. By calculating the The blood pressure difference between intervals is convenient for doctors to quickly understand the blood flow status of local blood vessels. In another example, the connection line between the first position of interest and the second position of interest may be generated according to the blood flow path of the vessel where the first position of interest and the second position of interest are located, so that the generated connection The line is closer to the real flow path of blood flow. Specifically, the blood flow path can be determined according to the vector blood flow velocity of the blood vessel where the first position of interest and the second position of interest are located, for example, the blood flow inflow position (the first position of interest or the second position of interest) is used as The starting point, based on the direction of the vector blood flow velocity of the starting point, select adjacent points, continue to find adjacent points based on the direction of the vector blood flow velocity of the adjacent point, and finally fit these points to the above-mentioned connection line. This method can accurately identify the real flow direction of blood flow, so it can more accurately describe the flow path of blood flow, provide more accurate positioning for subsequent measurement of blood pressure difference, and provide doctors with better judgment of blood flow status of local blood vessels. Accurate measurement indicators. In another example, the connecting line between the first location of interest and the second location of interest may be manually drawn by the user, for example, on the ultrasound image through a user interaction interface.

In step S130, for each interval, the vector blood flow velocity at the two ends of the interval and the interval length of the interval are obtained, and the interval is calculated based on the vector blood flow velocity and the interval length The difference in blood pressure between the two ends of the position.

In the embodiment of the present application, for each interval divided by the connecting line between the first position of interest and the second position of interest, the vector blood flow velocity at the two ends of the interval and the length to calculate the difference in blood pressure between the two ends of the interval. Such calculation is performed for each interval, and the blood pressure difference between the two ends of each interval can be obtained, so as to obtain the change of the pressure difference between the first location of interest and the second location of interest. For example, for the connection line between the first position of interest and the second position of interest, it can be divided into multiple line segments automatically or manually by the user, and for each line segment, the vector blood flow between the endpoints at both ends of the line segment is calculated The speed and the length of the line segment are used to calculate the blood pressure difference between the two ends of the line segment, so as to obtain the change of the pressure difference between the first position of interest and the second position of interest. Taking the example shown in FIG. 4 as an example, the change in pressure difference between the first location of interest A and the second location of interest B can be calculated by the following formula (1):

Wherein, i and j are the two endpoints of any interval on the line between the first position of interest A and the second position of interest B (for example, the distance between the first position of interest A and the second position of interest B The positions of two adjacent points on the connecting line), Δp _ij is the blood pressure difference between the two endpoints i and j of the interval, v _i and v _j are the respective vector blood flow velocities at the two endpoints i and j of the interval , l _ij is the length of the interval, ρ is the blood density (blood viscosity), and t is the time variable. When calculating the pressure difference between two points of interest based on formula (1), the influence of blood viscosity and the speed change between the two points AB and AB are not ignored. Compared with the calculation method described in the following examples (such as the formula ( 3) and formula (5)), the most accurate calculation result of local pressure difference can be obtained. However, when calculating the pressure difference between two locations of interest based on formula (1), the velocity of many points between the two locations of interest is required to be integrated. Only vector flow imaging technology can satisfy this precise pressure difference calculation. Way. Therefore, the measurement method 100 based on ultrasonic blood flow imaging according to the embodiment of the present application calculates the local vascular pressure difference based on the vector blood flow velocity, which can realize accurate calculation of the local pressure difference, and is non-invasive and fast.

In the embodiment of the present application, the vector blood flow velocity at the two ends of each interval can be calculated by the speckle tracking method, the transverse wave oscillation method or the multi-angle deflection transmission and/or reception method based on the Doppler principle . The vector blood flow velocity may include the magnitude of the velocity, and may also include the magnitude and direction of the velocity.

Wherein, taking the vector blood flow velocity obtained by the multi-angle deflection transmission/reception method as an example, the ultrasonic probe is used to transmit ultrasonic waves to the target blood flow area along the first scanning angle, and receive the ultrasonic echo of the ultrasonic wave returned from the target blood flow area . Obtain a first ultrasonic echo signal along the first scanning angle based on the ultrasonic echo, and obtain a first blood flow velocity at a target position (also called a target point) in the target blood flow area according to the first ultrasonic echo signal , the first blood flow velocity is actually a projection component (also referred to as a velocity component) of the vector blood flow velocity at the target position on the first scanning angle. Similarly, the second blood flow velocity at the target position can be obtained by transmitting ultrasonic waves to the target blood flow region through the ultrasonic probe along the second scanning angle, and the second blood flow velocity is actually the vector blood flow velocity of the target position at the target position. The projected component on the second scan angle (also called the velocity component). Angle synthesis is performed on the first blood flow velocity and the second blood flow velocity to obtain the actual magnitude and direction of the velocity, that is, the vector blood flow velocity.

As an example, the vector blood flow velocity can also be obtained based on the vector blood flow imaging method of speckle tracking. The vector blood flow velocity calculation of spot tracking can be realized by using the absolute difference summation. Among them, the vector blood flow velocity with higher precision can also be obtained based on plane wave emission and speckle tracking method.

As an example, the vector blood flow velocity can also be obtained by the vector blood flow imaging method based on the transverse wave oscillation method. Among them, the longitudinal velocity is obtained through the traditional calculation method based on the Doppler principle, the transverse velocity is calculated based on the autocorrelation method through the ultrasonic sound field that generates transverse oscillations, and then the vector blood flow velocity is obtained by combining the transverse and longitudinal velocities.

The velocity of the above-mentioned vector blood flow is the actual velocity of the blood flow (such as the red blood cells in the blood flow), or is closer to the actual velocity of the blood flow (such as the red blood cells in the blood flow); its velocity direction is the actual flow direction of the blood flow (such as the red blood cells in the blood flow), or closer to the actual flow direction of the blood flow (such as the red blood cells in the blood flow); the direction of the vector blood flow velocity can be from 0° to In the interval of 360°, its direction can represent the actual flow direction of the blood flow.

Based on the vector blood flow velocity at the two ends of each interval, a pressure gradient map between the first location of interest and the second location of interest can be generated to present the pressure gradient between the first location of interest and the second location of interest The variation trend of the blood pressure difference will be described in step S140.

In step S140, based on the magnitude of the blood pressure difference between the positions at both ends of each of the intervals, corresponding colors are displayed on different intervals of the connecting line, so as to present the first interest location and the second sense of interest. Trends in blood pressure differences between locations of interest.

In the embodiment of the present application, after calculating the blood pressure difference between the two ends of each interval of the line between the first position of interest and the second position of interest, you can The blood pressure difference between the two ends of each interval is marked with the corresponding color to generate a pressure gradient map reflecting the pressure drop trend between the first position of interest and the second position of interest, for example, as shown in Figure 4 of. In Figure 4, different pressure drop values in different intervals are presented in different colors. Here, it should be noted that due to the restriction that the accompanying drawings of the patent application documents cannot be color images, what is presented in Figure 4 is a grayscale image. In practical applications, the color atlas in Figure 4 can be a color atlas to more clearly reflect the two Pressure drop trends between locations of interest. In the example shown in FIG. 4 , the first location of interest A and the second location of interest are displayed in different colors on each section of the connecting line between the first location of interest A and the second location of interest The change trend of the pressure difference between B, such a display method can make the pressure drop of each interval clearly and correspondingly presented. Further, when the blood pressure difference in a certain section on the line is greater than a preset threshold, it is indicated that the blood flow corresponding to a certain section is abnormal. For example, different colors represent different pressure differences. Green indicates that the blood pressure difference corresponding to this interval is small, the blood flow is relatively smooth, and there is no obvious block or plaque, and red indicates that the blood pressure difference corresponding to this interval is relatively large. There may be plaque at the location, and doctors can quickly identify the status of blood vessels through color prompts, accurately locate abnormal locations, and improve diagnostic efficiency. In other examples, the pressure gradient map between the two locations of interest may also be presented in other ways, such as in the form of lines such as drawing graphs reflecting different pressure drops in different intervals.

In a further embodiment of the present application, the method 100 may further include (not shown): in response to the selected operation on the blood pressure difference between two ends of a certain interval on the line, displaying the corresponding blood pressure difference . In this embodiment, the pressure gradient map can realize user interaction. Through user selection, the blood pressure difference between the two ends of any interval on the line between two locations of interest can be further presented, which is beneficial for the user to While knowing the trend of pressure drop between two locations of interest, it can also obtain quantitative numerical results of blood pressure drop in any interval, which is more conducive to assisting doctors in diagnosis.

In general, the ultrasonic blood flow parameter measurement method 100 according to the embodiment of the present application calculates the local vascular pressure difference based on the vector blood flow velocity, which can realize accurate calculation of the local pressure difference, and is non-invasive and fast; in addition, according to the embodiment of the present application The measurement method of ultrasonic blood flow parameters generates a pressure gradient map between two positions of interest based on multiple vector blood flow velocities in the area between two positions of interest on the ultrasound image of the target vessel, which can realize Intuitive presentation of the change trend of differential pressure, accurately locate the abnormal position through different colors, and prompt the doctor to pay attention, so as to better assist the doctor in diagnosis.

The above exemplarily shows a method for measuring ultrasonic blood flow parameters according to an embodiment of the present application. The method for measuring ultrasonic blood flow parameters according to other embodiments of the present application will be described below with reference to FIGS. 5 to 10 .

Fig. 5 shows a schematic flowchart of a method 500 for measuring ultrasonic blood flow parameters according to another embodiment of the present application. As shown in FIG. 5, a method 500 for measuring ultrasonic blood flow parameters may include the following steps:

In step S510, a first position of interest and a second position of interest on the ultrasonic image of the target blood vessel are acquired.

In step S520, a connection line between the first location of interest and the second location of interest is determined, wherein the connection line includes a plurality of divided intervals.

In step S530, for each interval, the blood flow velocity at the two ends of the interval is obtained, and the blood pressure difference between the two ends of the interval is calculated based on the blood flow velocity.

In step S540, based on the magnitude of the blood pressure difference between the positions at both ends of each of the intervals, corresponding colors are displayed on different intervals of the connecting line, so as to present the first interest location and the second sense of interest. Trends in blood pressure differences between locations of interest.

In the embodiment of the present application, the method 500 for measuring ultrasonic blood flow parameters is partly similar to and partly different from the aforementioned method 100 for measuring ultrasonic blood flow parameters. Specifically, steps S510, S520, and S540 are the same as steps S110, S120, and S140, respectively, and there are only some differences between steps S530 and S130. For the sake of brevity, the same parts between the method 500 for measuring ultrasonic blood flow parameters here and the method 100 for measuring ultrasonic blood flow parameters described above will not be described in detail, and only the different parts between them will be described.

In the embodiment of the present application, after the measurement method 100 of ultrasonic blood flow parameters determines the line between the first position of interest and the second position of interest and its multiple intervals, in step S130 based on the two ends of each interval The vector blood flow velocity at the position and the interval length calculate the blood pressure difference between the positions at both ends of each interval, and the ultrasonic blood flow parameter measurement method 500 determines the connecting line between the first position of interest and the second position of interest After multiple intervals thereof, in step S530, based on the blood flow velocity at both ends of each interval (the blood flow velocity is not limited to the vector blood flow velocity or the blood flow velocity measured based on pulse Doppler, and there is no need to determine interval length) to calculate the blood pressure difference between the positions at both ends of each interval. Taking the example shown in FIG. 4 as an example, the blood pressure difference in any interval between the first location of interest A and the second location of interest B can be calculated by the following formula (2):

Wherein, i and j are the two endpoints of any interval on the line between the first position of interest A and the second position of interest B (for example, the distance between the first position of interest A and the second position of interest B Δp _ij is the blood pressure difference between the two endpoints i and j of the interval, and v _i and v _j are the respective blood flow velocities at the two endpoints i and j of the interval.

The blood pressure difference calculated based on the above formula ignores the influence of blood viscosity, and assumes blood viscosity as a constant. Because, for blood, although changes in blood flow velocity will lead to changes in blood viscosity, this change is relatively small and can be ignored. Compared with the calculation method in formula (1), the accuracy of such a calculation method may be reduced, but it is more convenient.

In an embodiment of the present application, the blood flow velocity acquired in step S530 may include a vector blood flow velocity or a blood flow velocity measured based on multi-point pulse Doppler. Wherein, the vector blood flow velocity can be calculated by speckle tracking method, transverse wave oscillation method or multi-angle deflection transmission and/or reception method based on the Doppler principle, which is similar to that described above and will not be repeated here. repeat. Finally, a pressure gradient map between the first location of interest and the second location of interest may be generated based on the blood flow velocities at the locations at both ends of each interval.

Based on the above description, the method 500 for measuring ultrasonic blood flow parameters according to an embodiment of the present application generates a pressure gradient between two positions of interest based on blood flow velocities at multiple places in the region between the two positions of interest on the ultrasound image of the target vessel The graph can realize the intuitive presentation of the pressure difference change trend between two locations of interest, so as to better assist doctors in diagnosis.

Fig. 6 shows a schematic flowchart of a method 600 for measuring ultrasonic blood flow parameters according to yet another embodiment of the present application. As shown in FIG. 6, a method 600 for measuring ultrasonic blood flow parameters may include the following steps:

In step S610, ultrasonic waves are transmitted to the target blood vessel along at least two different scanning angles, echoes of the ultrasonic waves are received, and at least two groups of ultrasonic echo signals are obtained based on the echoes of the ultrasonic waves, wherein each group of ultrasonic echo signals Ultrasonic waves emitted from a scanning angle.

In step S620, a first position of interest and a second position of interest on the ultrasound image of the target blood vessel, and a length between the first position of interest and the second position of interest are acquired.

In step S630, at least two velocity components at the first location of interest and at least two velocity components at the second location of interest are respectively obtained based on the at least two groups of ultrasonic echo signals, and each of the At least two velocity components at the positions of interest are synthesized to obtain a vector blood flow velocity at each position of interest, wherein each velocity component is derived from a set of ultrasonic echo signals.

In step S640, based on the vector blood flow velocity at the first location of interest, the vector blood flow velocity at the second location of interest, and the distance between the first location of interest and the second location of interest The length of is to calculate the blood pressure difference between the first location of interest and the second location of interest.

In the embodiment of the present application, the ultrasonic blood flow parameter measurement method 600 obtains the respective vector blood flow velocities of the first position of interest and the second position of interest on the ultrasonic image of the target blood vessel through a multi-angle deflection transmission/reception method. In the following, two scanning angles are taken as an example for description. The ultrasonic probe is used to transmit ultrasonic waves to the target blood flow area along the first scanning angle, and the ultrasonic echoes of the ultrasonic waves returned from the target blood flow area are received. Based on the ultrasonic echo, the first ultrasonic echo signal along the first scanning angle is obtained, and according to the first ultrasonic echo signal, the target position in the target blood flow area (including the first interest position in the embodiment of the present application) is obtained. and the first blood flow velocity of the second position of interest), the first blood flow velocity is actually the projected component of the vector blood flow velocity of the target position on the first scan angle (also called the velocity component) . Similarly, the second blood flow velocity at the target position can be obtained by transmitting ultrasonic waves to the target blood flow region through the ultrasonic probe along the second scanning angle, and the second blood flow velocity is actually the vector blood flow velocity of the target position at the target position. The projected component on the second scan angle (also called the velocity component). Angle synthesis is performed on the first blood flow velocity and the second blood flow velocity to obtain the actual magnitude and direction of the velocity, that is, the vector blood flow velocity. Through the above manner, the vector blood flow velocity at the first position of interest and the vector blood flow velocity at the second position of interest can be obtained respectively.

Based on the respective vector blood flow velocities of the first location of interest and the second location of interest and the length between the two locations, a blood pressure difference between the first location of interest and the second location of interest may be calculated. Similar to the previous embodiments, the connection line between the first position of interest and the second position of interest can be automatically generated according to the trends of the blood vessels where the first position of interest and the second position of interest are located, and based on the A connecting line determines the length between the first position of interest and the second position of interest; or, the first position of interest is generated according to the blood flow path of the vessel where the first position of interest and the second position of interest are located. A connection line between the location of interest and the second location of interest, and based on the connection, determine the length between the first location of interest and the second location of interest; or, obtain the user's A connecting line is drawn between the first location of interest and the second location of interest, and based on the connecting line, the length between the first location of interest and the second location of interest is determined. Taking the example shown in FIG. 2 as an example, the blood pressure difference between the first location of interest A and the second location of interest B can be calculated by the following formula (3):

Among them, Δp _AB is the blood pressure difference between the first location of interest A and the second location of interest B, v _A and v _B are the respective vector blood flow velocities of the first location of interest A and the second location of interest B , l _AB is the length between the first position of interest and the second position of interest, ρ is the blood density, and t is the time variable.

Therefore, according to the method 600 for measuring ultrasonic blood flow parameters according to the embodiment of the present application, the multi-angle deflection transmitting and/or receiving method based on the Doppler principle is used to calculate the vector blood flow velocities at two positions of interest in the ultrasonic image of the target blood vessel, And based on the vector blood flow velocity between the two positions of interest, the blood pressure difference between the two positions of interest can be calculated, which can realize accurate calculation of the local pressure difference, and is non-invasive and fast.

In a further embodiment of the present application, the method 600 for measuring ultrasonic blood flow parameters may further include the following steps (not shown): acquiring a third position of interest on the ultrasonic image of the target blood vessel, and the first The length between the position of interest and the third position of interest; the vector blood flow velocity at the third position of interest is obtained based on the at least two groups of ultrasonic echo signals; based on the position at the first position of interest The vector blood flow velocity at the third position of interest, the vector blood flow velocity at the third position of interest, and the length between the first position of interest and the third position of interest are used to calculate the relationship between the first position of interest and the The blood pressure difference between the third positions of interest is used as the second blood pressure difference; the blood pressure difference between the first position of interest and the second position of interest is used as the first blood pressure difference, and the first blood pressure difference is calculated and outputted. A difference between a first blood pressure difference and the second blood pressure difference.

In this embodiment, a third position of interest on the ultrasound image of the target blood vessel is also obtained, which will be described below with reference to FIG. 7 . As shown in FIG. 7 , the ultrasound image of the target blood vessel includes a first location of interest A, a second location of interest B, and a third location of interest C. Among them, the blood pressure difference between the first location of interest A and the second location of interest B can be calculated as the first blood pressure difference (as shown in the above formula (3)) by the method described above, and the same method is used Calculate the blood pressure difference between the first location of interest A and the third location of interest C as the second blood pressure difference, as shown in the following formula (4):

Among them, Δp _AC is the blood pressure difference between the first location of interest A and the third location of interest C, v _A and v _C are the respective vector blood flow velocities of the first location of interest A and the third location of interest C , l _AC is the length between the first position of interest and the third position of interest, ρ is the blood density, and t is the time variable.

In the example shown in FIG. 7 , a schematic diagram of a bifurcated blood vessel is shown, such as a carotid artery bifurcation, wherein the first location of interest A is in the common carotid artery, the second location of interest B is in the internal carotid artery, and the second location of interest B is in the internal carotid artery. The third location of interest C is in the external carotid artery. Therefore, the difference between the blood pressure difference between AB and AC can provide more reference data for doctors, so that doctors can understand the blood pressure difference in bifurcation vessels. Pressure drop comparison.

Fig. 8 shows a schematic flowchart of a method 800 for measuring ultrasonic blood flow parameters according to yet another embodiment of the present application. As shown in FIG. 8, a method 800 for measuring ultrasonic blood flow parameters may include the following steps:

In step S810, ultrasonic waves are transmitted to the target blood vessel along at least two different scanning angles, echoes of the ultrasonic waves are received, and at least two groups of ultrasonic echo signals are obtained based on the echoes of the ultrasonic waves, wherein each group of ultrasonic echo signals Ultrasonic waves emitted from a scanning angle.

In step S820, a first position of interest and a second position of interest on the ultrasound image of the target blood vessel are acquired.

In step S830, at least two velocity components at each position of interest are respectively obtained based on the at least two groups of ultrasonic echo signals, and at least two velocity components at each position of interest are synthesized to obtain each vector blood velocity at each of the locations of interest, wherein each velocity component is derived from a set of ultrasound echo signals.

In step S840, calculate the distance between the first position of interest and the second position of interest based on the vector blood flow velocity at the first position of interest and the vector blood flow velocity at the second position of interest poor blood pressure.

In the embodiment of the present application, the method 800 for measuring ultrasonic blood flow parameters is partly similar to and partly different from the aforementioned method 600 for measuring ultrasonic blood flow parameters. Specifically, steps S810 and S830 are different from steps S610 and S630, step S820 is different from step S620, and step S840 is different from step S640. For the sake of brevity, the same parts between the method 800 for measuring ultrasonic blood flow parameters and the method 600 for measuring ultrasonic blood flow parameters described above will not be described in detail, and only the different parts between them will be described.

In the embodiment of the present application, after the method 600 for measuring ultrasonic blood flow parameters obtains the first and second positions of interest in step S620, the distance between the first and second positions of interest also needs to be obtained. length, in step S640, the blood pressure difference between the two positions of interest is calculated based on the respective vector blood flow velocities at the two positions of interest and the length between the two positions of interest, and the method 800 for measuring ultrasonic blood flow parameters is After obtaining the first location of interest and the second location of interest in step S820, there is no need to obtain the length between the first location of interest and the second location of interest. In step S840, based on the respective vector blood flow velocities at the two locations of interest Computes the difference in blood pressure between two locations of interest. Using the example shown in Figure 2 to describe, the blood pressure difference between the first location of interest A and the second location of interest B can be calculated by the following formula (5):

Among them, Δp _AB is the blood pressure difference between the first location of interest A and the second location of interest B, v _A and v _B are the respective vector blood flow velocities of the first location of interest A and the second location of interest B .

The blood pressure difference calculated based on the above formula ignores the influence of blood viscosity, and assumes blood viscosity as a constant. Because, for blood, although changes in blood flow velocity will lead to changes in blood viscosity, this change is relatively small and can be ignored. Compared with the calculation method in formula (3), the accuracy of this calculation method may be reduced, but it is more convenient. In addition, the blood pressure difference calculated based on the above formula ignores the blood flow velocity change between the two points AB, so there may be a little error compared to the calculation method in formula (1), but it is more convenient. When calculating the pressure difference based on formula (5), it is necessary to measure the blood flow velocity at two positions simultaneously, which cannot be realized by traditional pulse Doppler. Blood flow velocity at the location.

Based on the above description, the ultrasonic blood flow parameter measurement method 800 according to the embodiment of the present application is based on the multi-angle deflection transmission and/or reception method of the Doppler principle to calculate the vector blood of the two interested positions of the ultrasonic image of the target blood vessel. Flow velocity, and calculate the blood pressure difference between the two locations of interest based on the vector blood flow velocity between the two locations of interest, can achieve accurate local pressure difference calculation, and non-invasive and fast.

In a further embodiment of the present application, the method 800 for measuring ultrasonic blood flow parameters may further include the following steps (not shown): acquiring a third position of interest on the ultrasonic image of the target blood vessel; The vector blood flow velocity at the third position of interest is obtained by grouping ultrasonic echo signals; the vector blood flow velocity at the first position of interest and the vector blood flow velocity at the third position of interest are calculated based on The blood pressure difference between the first location of interest and the third location of interest is used as the second blood pressure difference; the blood pressure difference between the first location of interest and the second location of interest is used as the first Blood pressure difference, calculating and outputting the difference between the first blood pressure difference and the second blood pressure difference.

In this embodiment, a third position of interest on the ultrasound image of the target blood vessel is also obtained, which can still be described in conjunction with FIG. 7 . As shown in FIG. 7 , the ultrasound image of the target blood vessel includes a first location of interest A, a second location of interest B, and a third location of interest C. Among them, the blood pressure difference between the first location of interest A and the second location of interest B can be calculated as the first blood pressure difference (as shown in the above formula (5)) by the method described above, and the same method Calculate the blood pressure difference between the first location of interest A and the third location of interest C as the second blood pressure difference, as shown in the following formula (6):

Among them, Δp _AC is the blood pressure difference between the first location of interest A and the third location of interest C, v _A and v _C are the respective vector blood flow velocities of the first location of interest A and the third location of interest C .

In the example shown in FIG. 7 , a schematic diagram of a bifurcated blood vessel is shown, such as a carotid artery bifurcation, wherein the first location of interest A is in the common carotid artery, the second location of interest B is in the internal carotid artery, and the second location of interest B is in the internal carotid artery. The third location of interest C is in the external carotid artery. Therefore, the difference between the blood pressure difference between AB and AC can provide more reference data for doctors, so that doctors can understand the blood pressure difference in bifurcation vessels. Pressure drop comparison.

Fig. 9 shows a schematic flowchart of a method 900 for measuring an ocular vascular index according to an embodiment of the present application. As shown in FIG. 9 , the method 900 for measuring the ocular vascular index may include the following steps:

In step S910, the blood pressure difference between the first position of interest and the second position of interest on the ultrasonic image of the target blood vessel is obtained, wherein the first position of interest and the second position of interest are respectively located in the common carotid artery and internal carotid artery.

In step S920, blood flow parameters of ocular blood vessels connected with the internal carotid artery are acquired, and the blood flow parameters include peak systolic flow velocity and end-diastolic flow velocity.

In step S930, the velocity difference between the systolic peak flow velocity and the end-diastolic flow velocity is calculated, and the ratio of the blood pressure difference to the velocity difference is calculated and output.

In the embodiment of the present application, the method 900 for measuring ocular vascular index combined with internal carotid artery pressure difference to calculate the ocular vascular index can provide doctors with clinical research and related diagnosis of eye diseases, especially ischemic eye diseases , detailed later. Wherein, the pressure difference of the internal carotid artery refers to the pressure difference between the common carotid artery and the internal carotid artery, so the acquired first position of interest and the second position of interest are respectively located in the common carotid artery and the internal carotid artery, The calculation of the blood pressure difference between the first location of interest and the second location of interest can be as described in the previous embodiments.

In one embodiment, acquiring the blood pressure difference between the first position of interest and the second position of interest on the ultrasound image of the target blood vessel in step S910 may include: acquiring the first sense of interest on the ultrasound image of the target blood vessel The respective vector blood flow velocities at the position of interest and the second position of interest, and the length between the first position of interest and the second position of interest; based on the vector blood flow velocity at the first position of interest, The vector blood flow velocity at the second location of interest and the length between the first location of interest and the second location of interest calculate the distance between the first location of interest and the second location of interest The blood pressure difference between them is shown in formula (3) above.

In another embodiment, acquiring the blood pressure difference between the first position of interest and the second position of interest on the ultrasonic image of the target blood vessel in step S910 may include: acquiring the first position of interest on the ultrasonic image of the target blood vessel The respective blood flow velocities at the location of interest and the second location of interest; calculating the first location of interest based on the blood flow velocity at the first location of interest and the blood flow velocity at the second location of interest The blood pressure difference with the second position of interest is shown in formula (5) above.

In yet another embodiment, acquiring the blood pressure difference between the first position of interest and the second position of interest on the ultrasonic image of the target blood vessel in step S910 may include: acquiring the first position of interest on the ultrasonic image of the target blood vessel The blood flow velocity at the maximum stenosis of the internal carotid artery between the position of interest and the second position of interest; the first position of interest and the second sense of interest are calculated based on the blood flow velocity at the maximum stenosis of the internal carotid artery The blood pressure difference between the positions of interest, the calculation method in this embodiment can be as shown in formula (7):

Wherein, Δp is the blood pressure difference between the first location of interest and the second location of interest, and v _max is the blood flow velocity at the maximum stenosis of the internal carotid artery between the first location of interest and the second location of interest. The blood pressure difference calculated based on formula (7) ignores the influence of blood viscosity, assumes blood viscosity as a constant, and also ignores the change of blood flow velocity between two interested locations, and is based on certain assumptions. The blood flow velocity in the stenosis is much higher than that in normal blood vessels. Such a calculation method may have lower accuracy than the calculation method described above, but it is more convenient, because it only needs to measure the maximum blood flow velocity, which can be realized by traditional pulse Doppler.

Therefore, in the embodiment of the present application, the measurement method 900 based on ultrasonic blood flow imaging can be based on blood flow velocity measured by traditional pulse Doppler method, blood flow velocity measured by multi-point pulse Doppler or Calculate the internal carotid artery pressure by vector blood flow velocity (wherein, the vector blood flow velocity is calculated by speckle tracking method, transverse wave oscillation method or multi-angle deflection transmission and/or reception method based on Doppler principle) Difference. Since the ophthalmic artery is a branch of the internal carotid artery, when there is a large pressure drop in the carotid sinus, especially when there is a large pressure difference between the common carotid artery and the internal carotid artery, it may affect the distal ophthalmic artery. supply blood. Therefore, the method 900 for measuring the ocular vascular index can calculate a parameter related to the blood supply to the eye based on the pressure drop at the carotid sinus. It will be described below in conjunction with FIG. 10 .

As shown in Figure 10, the bifurcation of the carotid artery is shown, the first position of interest A is in the common carotid artery, the second position of interest B is in the internal carotid artery, there is stenosis or plaque in the carotid, the internal carotid artery and the eye arterial connection. The line AB crosses the internal carotid artery plaque, or across the internal carotid artery stenosis, and then the pressure drop value Δp between AB and AB is obtained. Then, by measuring the blood flow velocity of the eye vessels by means of ultrasound (such as based on the pulse Doppler method), the blood flow parameters of at least one of the ophthalmic artery, the central retinal artery, and the ciliary artery can be obtained. Including peak systolic velocity (PSV) and end-diastolic velocity (EDV). The new parameters can be calculated by the following formula (8):

Wherein, the higher the Q value, the greater the possibility of ischemia in the ocular blood vessels, and/or the greater the correlation between the cause of ischemia and carotid artery stenosis. The lower the Q value, the less likely there is ischemia in the ocular blood vessels, or the less affected by carotid artery stenosis.

In a further embodiment of the present application, the method 900 for measuring the ocular vascular index may also include the following steps (not shown): comparing the ratio (that is, the aforementioned Q value) with a preset threshold, and according to the comparison As a result, prompt information is output; when the ratio is greater than the preset threshold, the prompt information includes: there is a high possibility of ischemia in the eye vessels, and/or the cause of ischemia is highly related to carotid artery stenosis; when the When the ratio is smaller than the preset threshold, the prompt information includes: the possibility of ischemia in the eye vessels is low, or the cause of the ischemia has little correlation with carotid artery stenosis.

Therefore, the method 900 for measuring ocular vascular index according to the embodiment of the present application calculates a parameter related to ocular blood supply based on the pressure drop at the carotid sinus, which can provide doctors with ocular diseases, especially ischemic ocular Clinical research and associated diagnosis of disease.

The above exemplarily shows the measurement method of the ultrasonic blood flow parameter and the ocular blood vessel index according to the embodiment of the present application. The ultrasonic blood flow imaging device provided according to another aspect of the present application will be described below with reference to FIG. 11 . Fig. 11 shows a schematic structural block diagram of an ultrasonic blood flow imaging device 1100 according to an embodiment of the present application. As shown in Figure 11, the ultrasonic blood flow imaging device 1100 includes a transmitting circuit 1120, a receiving circuit 1130, an ultrasonic probe 1110, a processor 1140 and a display 1150, wherein: the transmitting circuit 1120 is used to control the ultrasonic probe 1110 to transmit Ultrasound: the receiving circuit 1130 is used to control the ultrasonic probe 1110 to receive the echo of the ultrasonic wave, and obtain an ultrasonic echo signal from the echo of the ultrasonic wave; the processor 1140 is used to perform ultrasonic blood flow imaging based on the ultrasonic echo signal , is also used to execute the method for measuring ultrasonic blood flow parameters or ocular vascular index according to the embodiment of the present application described above; the display 1150 is used to display the result output by the processor 1140 . Those skilled in the art can understand the structure and operation of the ultrasonic blood flow imaging device 1100 according to the embodiment of the present application in combination with the foregoing description about the measurement method of the ultrasonic blood flow parameter or the ocular vascular index according to the embodiment of the present application. For the sake of brevity, The specific detailed operations of the components of the ultrasonic blood flow imaging device 1100 will not be repeated here.

Based on the above description, according to the embodiment of the present application, the ultrasonic blood flow parameters, the measurement method of the eye vascular index and the ultrasonic blood flow imaging device calculate the local blood vessel pressure difference based on the vector blood flow velocity, which can realize accurate local pressure difference calculation, and Non-invasive and fast; in addition, the method for measuring ultrasonic blood flow parameters according to the embodiment of the present application generates the pressure between two positions of interest based on multiple vector blood flow velocities in the area between two positions of interest on the ultrasonic image of the target vessel Gradient map, which can realize the intuitive presentation of the trend of pressure difference between two locations of interest, so as to better assist doctors in diagnosis; in addition, the measurement method based on ocular vascular index calculates a pressure drop based on the carotid sinus Parameters related to eye blood supply can provide doctors with clinical research and related diagnosis of eye diseases, especially ischemic eye diseases.

Although example embodiments have been described herein with reference to the accompanying drawings, it should be understood that the above-described example embodiments are exemplary only, and are not intended to limit the scope of the application thereto. Various changes and modifications can be made therein by those of ordinary skill in the art without departing from the scope and spirit of the application. All such changes and modifications are intended to be included within the scope of this application as claimed in the appended claims.

Those skilled in the art can appreciate that the units and algorithm steps of the examples described in conjunction with the embodiments disclosed herein can be implemented by electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are executed by hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art may use different methods to implement the described functions for each specific application, but such implementation should not be regarded as exceeding the scope of the present application.

In the several embodiments provided in this application, it should be understood that the disclosed devices and methods may be implemented in other ways. For example, the device embodiments described above are only illustrative. For example, the division of the units is only a logical function division. In actual implementation, there may be other division methods. For example, multiple units or components can be combined or May be integrated into another device, or some features may be omitted, or not implemented.

In the description provided herein, numerous specific details are set forth. However, it is understood that the embodiments of the application may be practiced without these specific details. In some instances, well-known methods, structures and techniques have not been shown in detail in order not to obscure the understanding of this description.

Similarly, it should be understood that in the description of the exemplary embodiments of the application, in order to streamline the application and to facilitate understanding of one or more of the various inventive aspects, various features of the application are sometimes grouped together into a single embodiment, figure , or in its description. This method of application, however, is not to be interpreted as reflecting an intention that the claimed application requires more features than are expressly recited in each claim. Rather, as the corresponding claims reflect, the inventive point lies in that the corresponding technical problem may be solved by using less than all features of a single disclosed embodiment. Thus, the claims following this Detailed Description are hereby expressly incorporated into this Detailed Description, with each claim standing on its own as a separate embodiment of this application.

It will be appreciated by those skilled in the art that all features disclosed in this specification (including accompanying claims, abstract and drawings) and all features of any method or apparatus so disclosed may be used in any combination, except where the features are mutually exclusive. process or unit. Each feature disclosed in this specification (including accompanying claims, abstract and drawings) may be replaced by alternative features serving the same, equivalent or similar purpose, unless expressly stated otherwise.

In addition, those skilled in the art will appreciate that although some embodiments described herein include some features included in other embodiments but not others, combinations of features from different embodiments are meant to be within the scope of the present application. and form different embodiments. For example, in the claims, any one of the claimed embodiments can be used in any combination.

The various component embodiments of the present application may be realized in hardware, or in software modules running on one or more processors, or in a combination thereof. Those skilled in the art should understand that a microprocessor or a digital signal processor (DSP) may be used in practice to implement some or all functions of some modules in the item analysis device according to the embodiment of the present application. The present application can also be implemented as an ultrasound blood flow imaging device program (for example, a computer program and a computer program product) for performing a part or all of the methods described herein. Such a program implementing the present application may be stored on a computer-readable medium, or may be in the form of one or more signals. Such a signal may be downloaded from an Internet site, or provided on a carrier signal, or provided in any other form.

It should be noted that the above-mentioned embodiments illustrate rather than limit the application, and that those skilled in the art will be able to design alternative embodiments without departing from the scope of the appended claims. In the claims, any reference signs placed between parentheses shall not be construed as limiting the claim. The word "comprising" does not exclude the presence of elements or steps not listed in a claim. The word "a" or "an" preceding an element does not exclude the presence of a plurality of such elements. The application can be implemented by means of hardware comprising several distinct elements, and by means of a suitably programmed computer. In the unit claim listing several ultrasonic blood flow imaging devices, several of these ultrasonic blood flow imaging devices may be embodied by the same hardware item. The use of the words first, second, and third, etc. does not indicate any order. These words can be interpreted as names.

The above is only the specific implementation of the application or the description of the specific implementation. The scope of protection of the application is not limited thereto. Any person familiar with the technical field can easily Any changes or substitutions that come to mind should be covered within the protection scope of the present application. The protection scope of the present application should be based on the protection scope of the claims.

Claims (19)

1. A method of measuring an ultrasonic blood flow parameter, the method comprising:

acquiring a first interest position and a second interest position on an ultrasonic image of a target blood vessel;

determining a line between the first location of interest and the second location of interest, wherein the line comprises a plurality of divided intervals;

for each interval, acquiring vector blood flow velocities at positions at two ends of the interval and an interval length of the interval, and calculating a blood pressure difference between the positions at the two ends of the interval based on the vector blood flow velocities and the interval length;

displaying corresponding colors on different sections of the connecting line based on the magnitude of the blood pressure difference between the two end positions of each section so as to present the variation trend of the blood pressure difference between the first interest position and the second interest position.

2. A method of measuring an ultrasonic blood flow parameter, the method comprising:

acquiring a connecting line drawn on an ultrasonic image of a target blood vessel by a user, wherein the connecting line comprises a plurality of divided intervals;

for each interval, acquiring vector blood flow velocities at positions at two ends of the interval and an interval length of the interval, and calculating a blood pressure difference between the positions at the two ends of the interval based on the vector blood flow velocities and the interval length;

and displaying corresponding colors on different sections of the connecting line based on the magnitude of the blood pressure difference between the two end positions of each section so as to present the variation trend of the blood pressure difference on the connecting line.

3. The method according to claim 1 or 2, wherein the vector blood flow velocity is calculated by a speckle tracking method, a transverse wave oscillation method, or a multi-angle deflection transmitting and/or receiving method based on the doppler principle.

4. The method of claim 1, wherein determining the connection between the first location of interest and the second location of interest comprises:

and automatically generating a connecting line between the first interesting position and the second interesting position according to the trend of the blood vessel in which the first interesting position and the second interesting position are positioned.

5. The method of claim 1, wherein determining the connection between the first location of interest and the second location of interest comprises:

generating a connecting line between the first and second locations of interest from a blood flow path of a blood vessel in which the first and second locations of interest are located.

6. The method according to claim 1 or 2, characterized in that the method further comprises:

in response to a selected manipulation of the blood pressure difference for an interval on the line, a corresponding blood pressure difference value is displayed.

7. The method according to claim 1 or 2, wherein when the magnitude of the blood pressure difference of a certain interval on the connection line is larger than a preset threshold value, it is indicated that the blood flow corresponding to the certain interval is abnormal.

8. A method of measuring an ultrasonic blood flow parameter, the method comprising:

transmitting ultrasonic waves to a target blood vessel along at least two different scanning angles, receiving echoes of the ultrasonic waves, and obtaining at least two groups of ultrasonic echo signals based on the echoes of the ultrasonic waves, wherein each group of ultrasonic echo signals is derived from the ultrasonic waves transmitted at one scanning angle;

acquiring a first position of interest and a second position of interest on an ultrasound image of the target vessel, and a length between the first position of interest and the second position of interest;

obtaining at least two velocity components at the first interest position and at least two velocity components at the second interest position respectively based on the at least two groups of ultrasonic echo signals, and synthesizing the at least two velocity components at each interest position to obtain a vector blood flow velocity at each interest position, wherein each velocity component is derived from one group of ultrasonic echo signals;

calculating a blood pressure difference between the first location of interest and the second location of interest based on the vector blood flow velocity at the first location of interest, the vector blood flow velocity at the second location of interest, and the length between the first location of interest and the second location of interest.

9. The method of claim 8, wherein the obtaining a length between the first location of interest and the second location of interest comprises:

and automatically generating a connecting line between the first interest position and the second interest position according to the trend of the blood vessel in which the first interest position and the second interest position are positioned, and determining the length between the first interest position and the second interest position based on the connecting line.

10. The method of claim 8, wherein the obtaining a length between the first location of interest and the second location of interest comprises:

generating a connecting line between the first interest position and the second interest position according to the blood flow path of the blood vessel in which the first interest position and the second interest position are located, and determining the length between the first interest position and the second interest position based on the connecting line.

11. The method according to any one of claims 8-10, further comprising:

acquiring a third location of interest on an ultrasound image of the target vessel and a length between the first location of interest and the third location of interest;

obtaining a vector blood flow velocity at the third location of interest based on the at least two sets of ultrasound echo signals;

calculating a blood pressure difference between the first location of interest and the third location of interest as a second blood pressure difference based on the vector blood flow velocity at the first location of interest, the vector blood flow velocity at the third location of interest, and the length between the first location of interest and the third location of interest;

calculating and outputting a difference between the first blood pressure difference and the second blood pressure difference, taking a blood pressure difference between the first interest location and the second interest location as a first blood pressure difference.

12. A method of measuring an ocular vascular index, the method comprising:

acquiring a blood pressure difference between a first interest position and a second interest position on an ultrasonic image of a target blood vessel, wherein the first interest position and the second interest position are respectively positioned in a common carotid artery and an internal carotid artery;

obtaining blood flow parameters of an ocular vessel communicating with the internal carotid artery, the blood flow parameters including a peak systolic flow rate and an end diastolic flow rate;

calculating a velocity difference between the peak systolic flow rate and the end diastolic flow rate, and calculating and outputting a ratio of the blood pressure difference to the velocity difference.

13. The method of claim 12, wherein the obtaining a blood pressure difference between a first location of interest and a second location of interest on an ultrasound image of a target vessel comprises:

acquiring respective vector blood flow velocities at a first and a second location of interest on an ultrasound image of the target vessel, and a length between the first and second location of interest;

calculating a blood pressure difference between the first and second locations of interest based on the vector blood flow velocity at the first location of interest, the vector blood flow velocity at the second location of interest, and the length between the first and second locations of interest.

14. The method of claim 12, wherein the obtaining a blood pressure difference between a first location of interest and a second location of interest on an ultrasound image of a target vessel comprises:

simultaneously obtaining respective blood flow velocities at a first interest position and a second interest position on an ultrasonic image of the target blood vessel based on a multipoint pulse Doppler method;

calculating a blood pressure difference between the first and second locations of interest based on the blood flow velocity at the first and second locations of interest.

15. The method of claim 12, wherein the obtaining a blood pressure difference between a first location of interest and a second location of interest on an ultrasound image of a target vessel comprises:

acquiring a blood flow velocity at a maximum stenosis of an internal carotid artery between a first interest position and a second interest position on an ultrasound image of the target vessel;

calculating a blood pressure difference between the first and second locations of interest based on a blood flow velocity at the maximum narrowing of the internal carotid artery.

16. The method according to any one of claims 12 to 15, further comprising:

comparing the ratio with a preset threshold value, and outputting prompt information according to a comparison result;

when the ratio is greater than a preset threshold, the prompt message includes: the ocular vessels are highly likely to have ischemia, and/or the cause of ischemia is highly correlated with carotid stenosis;

when the ratio is smaller than a preset threshold, the prompt message includes: the ocular vessels are less likely to have ischemia, or the cause of ischemia is less associated with carotid stenosis.

17. The method of any one of claims 12 to 15, wherein the peak systolic flow rate and the end diastolic flow rate are blood flow velocities measured based on pulse doppler.

18. The method of any one of claims 12 to 15, wherein the ocular vessel comprises at least one of an ocular artery, a central retinal artery, a ciliary artery.

19. An ultrasonic blood flow imaging apparatus, comprising a transmitting circuit, a receiving circuit, an ultrasonic probe, a processor and a display, wherein:

the transmitting circuit is used for controlling the ultrasonic probe to transmit ultrasonic waves to a target part of a target object;

the receiving circuit is used for controlling the ultrasonic probe to receive the echo of the ultrasonic wave and acquiring an ultrasonic echo signal from the echo of the ultrasonic wave;

the processor is used for carrying out ultrasonic blood flow imaging based on the ultrasonic echo signal;

the processor is further configured to perform the method of measuring an ultrasound blood flow parameter of any one of claims 1-18;

the display is used for displaying the result output by the processor.

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