Blood flow velocity vector imaging method, ultrasonic imaging method and ultrasonic imaging device

Abstract

The embodiment of the invention discloses a blood flow velocity vector imaging method, an ultrasonic imaging method and an ultrasonic imaging device, and the method comprises the steps: controlling at least two ultrasonic array element groups on an ultrasonic probe to emit non-focused ultrasonic waves in different emission directions, receiving an echo signal, obtaining a blood flow velocity component according to the echo signal, and carrying out the reconstruction. The blood flow velocity vector of the target area is obtained. And each ultrasonic array element group comprises a plurality of array elements distributed at different positions. Compared with the mode that the same ultrasonic array element group is adopted to emit the ultrasonic waves at different angles to conduct blood flow velocity vector detection, the positions, distributed on the ultrasonic probe, of the array elements of the ultrasonic array element groups corresponding to different emission directions are staggered, and therefore the overlapping range of the non-focused ultrasonic waves emitted by all the ultrasonic array element groups can be enlarged, and the detection accuracy of the blood flow velocity vector is improved. Therefore, the coverage range of blood flow velocity vector imaging is expanded.

Description

Technical Field

[0001] The embodiments of the present application relate to the field of ultrasonic imaging, and in particular to a blood flow velocity vector imaging method, an ultrasonic imaging method, and an ultrasonic imaging device. Background Art

[0002] Medical ultrasonic imaging diagnostic equipment uses the propagation of ultrasonic waves in the human body to obtain ultrasonic characteristic information of human tissue and organ structure. It has the advantages of being non-invasive, real-time, and low-cost, and is widely used in the field of auxiliary diagnosis of cardiovascular diseases. In order to more accurately evaluate the blood flow status of patients with cardiovascular diseases, a commonly used method is blood flow velocity vector imaging, which uses the blood flow velocity vector imaging method to calculate the actual size and direction of the blood flow velocity to display the blood flow velocity vector image. Among them, multi-angle ultrasonic emission scanning can be used to obtain velocity components in different directions of the target position, and then the blood flow vector is obtained by vector synthesis of these velocity components.

[0003] At present, ultrasound waves at different angles are emitted by the same ultrasound array element on the ultrasound probe. Therefore, the detection range of the blood flow velocity vector is the range covered by ultrasound waves at different angles. To expand the coverage range of ultrasound waves at different angles, it is necessary to increase the number of array elements on the ultrasound probe that emit ultrasound waves. However, since there is an upper limit on the number of system channels supported by the ultrasound imaging system, when the number of ultrasound probe array elements exceeds the number of ultrasound system channels, not all ultrasound array elements can be used to emit ultrasound waves. Therefore, the scanning area, especially the scanning area with multiple angles overlapping, will be much smaller than when all array elements are emitted, thereby causing the imaging area to become smaller, affecting clinical research and diagnosis. Summary of the invention

[0004] The following is an overview of the subject matter described in detail herein. This overview is not intended to limit the scope of protection of the claims. The embodiments of the present application provide a blood flow velocity vector imaging method, an ultrasound imaging method, and an ultrasound imaging device, which can expand the coverage of blood flow velocity vector imaging when full array element transmission cannot be achieved.

[0005] In a first aspect, an embodiment of the present application provides a blood flow velocity vector imaging method, the method comprising:

[0006] Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe by a front-end transceiver circuit to transmit non-focused ultrasonic waves to the target area in different transmission directions, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein one group of the ultrasonic array element groups corresponds to one transmission direction, each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and each group of the ultrasonic array element groups includes a plurality of array elements at the same position and at least one array element at a different position distributed on the ultrasonic probe;

[0007] Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction;

[0008] According to at least two groups of echo signals of the non-focused ultrasound, at least two blood flow velocity components corresponding to different emission directions are obtained, wherein one of the emission directions corresponds to one of the blood flow velocity components;

[0009] Reconstructing the velocity of the at least two blood flow velocity components in different emission directions to obtain blood flow velocity vector data of the target area;

[0010] obtaining a blood flow velocity vector image of the target area based on the blood flow velocity vector data of the target area;

[0011] The blood flow velocity vector image is displayed.

[0012] In a second aspect, an embodiment of the present application provides a blood flow velocity vector imaging method, the method comprising:

[0013] Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe to transmit non-focused ultrasonic waves to the target area in different transmission directions respectively through the front-end transceiver circuit, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and the positions of the plurality of array elements included in at least two groups of the ultrasonic array element groups on the ultrasonic probe are completely different;

[0014] Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction;

[0015] According to at least two groups of echo signals of the non-focused ultrasound, at least two blood flow velocity components corresponding to different emission directions are obtained, wherein one of the emission directions corresponds to one of the blood flow velocity components;

[0016] Reconstructing the velocity of the at least two blood flow velocity components in different emission directions to obtain blood flow velocity vector data of the target area;

[0017] obtaining a blood flow velocity vector image of the target area based on the blood flow velocity vector data of the target area;

[0018] The blood flow velocity vector image is displayed.

[0019] In a third aspect, an embodiment of the present application provides an ultrasonic imaging method, the method comprising:

[0020] Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe by a front-end transceiver circuit to transmit non-focused ultrasonic waves to the target area in different transmission directions, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and each group of the ultrasonic array element groups includes a plurality of array elements at the same position distributed on the ultrasonic probe and at least one array element at a different position;

[0021] Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction;

[0022] Compounding at least two groups of non-focused ultrasonic echo signals to obtain a compounded echo signal;

[0023] An ultrasonic image or blood flow velocity is obtained according to the composite echo signal.

[0024] In a fourth aspect, an embodiment of the present application provides an ultrasonic imaging method, the method comprising:

[0025] Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe to transmit non-focused ultrasonic waves to the target area in different transmission directions respectively through the front-end transceiver circuit, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and the positions of the plurality of array elements included in at least two groups of the ultrasonic array element groups on the ultrasonic probe are completely different;

[0026] Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction;

[0027] Compounding at least two groups of non-focused ultrasonic echo signals to obtain a compounded echo signal;

[0028] An ultrasonic image or blood flow velocity is obtained according to the composite echo signal.

[0029] In a fifth aspect, an embodiment of the present application provides an ultrasonic imaging device, comprising:

[0030] Ultrasound probe;

[0031] a transmitting / receiving circuit, the transmitting / receiving circuit being used to control the ultrasonic probe to transmit ultrasonic waves to a blood vessel region of a target object and to receive echoes of the ultrasonic waves;

[0032] A processor, the processor being used to process the ultrasonic echo to obtain a tissue image and / or a blood flow velocity vector image of the blood vessel region;

[0033] A display, the display being used to display the tissue image and / or the blood flow velocity vector image;

[0034] The processor is further configured to execute the blood flow velocity vector imaging method described in any one of the above embodiments, or execute the ultrasound imaging method described in any one of the above embodiments.

[0035] In a sixth aspect, an embodiment of the present application provides an electronic device, comprising a memory and a processor, wherein the memory stores a computer program, and when the processor executes the computer program, the blood flow velocity vector imaging method as described in any one of the above embodiments is implemented, or the ultrasound imaging method as described in any one of the above embodiments is executed.

[0036] In the seventh aspect, an embodiment of the present application provides a computer storage medium having a computer program stored thereon, which is applied to an ultrasonic imaging device. When the computer program is executed by a processor, it implements the ultrasonic transmission method of the first, third or fifth aspect embodiments mentioned above, or is also used to execute the blood flow velocity vector imaging method described in any one of the above embodiments, or execute the ultrasonic imaging method described in any one of the above embodiments.

[0037] In an eighth aspect, an embodiment of the present application provides a computer program product or a computer program, the computer program product or the computer program including computer instructions, the computer instructions being stored in a computer-readable storage medium. A processor of a computer device reads the computer instructions from the computer-readable storage medium, and the processor executes the computer instructions, so that the computer device executes the blood flow velocity vector imaging method as described in any one of the above embodiments, or executes the ultrasound imaging method as described in any one of the above embodiments.

[0038] In some embodiments of the present application, the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasound probe, and the front-end transceiver circuit controls at least two groups of ultrasound array elements on the ultrasound probe to transmit non-focused ultrasound to the target area in different transmission directions, and the front-end transceiver circuit controls the ultrasound probe to receive the echo of the non-focused ultrasound returned by the target area, so as to obtain at least two groups of echo signals of non-focused ultrasound corresponding to different transmission directions, and obtain at least two blood flow velocity components corresponding to different transmission directions according to the echo signals of the at least two groups of non-focused ultrasound, and reconstruct the at least two blood flow velocity components to obtain the blood flow velocity vector of the target area. Each group of ultrasound array elements includes a plurality of array elements distributed on the ultrasound probe that are less than or equal to the number of all transceiver channels, and each group of ultrasound array elements has a plurality of array elements at the same position and at least one array element at a different position distributed on the ultrasound probe. Compared with using the same ultrasound array element group to transmit ultrasound waves in different directions for blood flow velocity vector detection, in the embodiment of the present application, since the array elements of the ultrasound array element group corresponding to different emission directions are distributed at positions staggered on the ultrasound probe, it is possible to increase the overlapping range of non-focused ultrasound waves emitted by each of the ultrasound array element groups in different emission directions without increasing the number of array elements of the ultrasound array element group and the number of transceiver channels, thereby improving the coverage range of blood flow velocity vector imaging.

[0039] In some embodiments of the present application, the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasound probe, and the front-end transceiver circuit controls at least two groups of ultrasound array elements on the ultrasound probe to transmit non-focused ultrasound to the target area in different transmission directions respectively, and the front-end transceiver circuit controls the ultrasound probe to receive the echo of the non-focused ultrasound returned by the target area to obtain at least two groups of echo signals of non-focused ultrasound corresponding to different transmission directions, and obtains at least two blood flow velocity components corresponding to different transmission directions according to the echo signals of the at least two groups of non-focused ultrasound, and reconstructs the at least two blood flow velocity components to obtain the blood flow velocity vector of the target area. Each group of ultrasound array elements includes a number of array elements distributed on the ultrasound probe that is less than or equal to the number of all transceiver channels, and the positions of the multiple array elements included in at least two groups of ultrasound array elements on the ultrasound probe are completely different. Compared with using the same ultrasound array element group to transmit ultrasound waves at different angles for blood flow velocity vector detection, in the embodiment of the present application, since the array elements of the ultrasound array element group corresponding to different emission directions are distributed at positions staggered on the ultrasound probe, it is possible to increase the overlapping range of non-focused ultrasound waves emitted by each of the ultrasound array element groups in different emission directions without increasing the number of array elements of the ultrasound array element group and the number of transceiver channels, thereby improving the coverage range of blood flow velocity vector imaging. BRIEF DESCRIPTION OF THE DRAWINGS

[0040] The accompanying drawings are used to provide further understanding of the technical solution of the present application and constitute a part of the specification. Together with the embodiments of the present application, they are used to explain the technical solution of the present application and do not constitute a limitation on the technical solution of the present application.

[0041] Figure 1 It is a schematic diagram of an ultrasound probe emitting ultrasound waves in a scene;

[0042] Figure 2 It is a schematic diagram of an ultrasound probe emitting ultrasound waves in another scenario;

[0043] Figure 3 is a schematic structural diagram of an ultrasonic imaging device provided by an embodiment of the present application;

[0044] Figure 4 is a flow chart of a blood flow velocity vector imaging method provided by an embodiment of the present application;

[0045] Figure 5a is a schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0046] Figure 5b is a schematic diagram of an ultrasonic probe emitting ultrasonic waves provided by another embodiment of the present application;

[0047] Figure 5c is a schematic diagram of an ultrasonic probe emitting ultrasonic waves provided by another embodiment of the present application;

[0048] Figure 6 It is a schematic diagram of velocity reconstruction of blood flow velocity components provided by an embodiment of the present application;

[0049] Figure 7 is a timing diagram of an ultrasonic probe emitting ultrasonic waves provided by another embodiment of the present application;

[0050] Figure 8 is a flowchart of specific steps of step 412 provided in one embodiment of the present application;

[0051] Figure 9a is a schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0052] Figure 9b is a schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0053] Fig.9c A schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0054] Figure 9d A schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0055] Fig.9e A schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0056] Fig.10 is a flowchart of specific steps of step 412 provided in one embodiment of the present application;

[0057] Fig.11a is a schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0058] Fig.11b is a schematic diagram of an ultrasonic probe transmitting ultrasonic waves provided by an embodiment of the present application;

[0059] Fig.12 It is a flow chart of an ultrasound imaging method provided by an embodiment of the present application. DETAILED DESCRIPTION

[0060] The present application is further described below in conjunction with the accompanying drawings and specific embodiments. The described embodiments should not be regarded as limiting the present application, and all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present application.

[0061] In the following description, reference is made to “some embodiments”, which describe a subset of all possible embodiments, but it can be understood that “some embodiments” may be the same subset or different subsets of all possible embodiments and may be combined with each other without conflict.

[0062] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as those commonly understood by those skilled in the art to which this application belongs. The terms used herein are only for the purpose of describing the embodiments of this application and are not intended to limit this application.

[0063] Medical ultrasonic imaging diagnostic equipment uses the propagation of ultrasonic waves in the human body to obtain ultrasonic characteristic information of human tissue and organ structure. It has the advantages of being non-invasive, real-time, and low-cost, and is widely used in the field of auxiliary diagnosis of cardiovascular diseases. In order to more accurately evaluate the blood flow status of patients with cardiovascular diseases, a commonly used method is blood flow velocity vector imaging, which uses the blood flow velocity vector imaging method to calculate the actual size and direction of the blood flow velocity to display the blood flow velocity vector image. Among them, multi-angle ultrasonic emission scanning can be used to obtain velocity components in different directions of the target position, and then the blood flow vector is obtained by vector synthesis of these velocity components.

[0064] At present, ultrasound waves at different angles are emitted by the same ultrasound array element on the ultrasound probe. Therefore, the detection range of the blood flow velocity vector is the range covered by ultrasound waves at different angles. To expand the coverage range of ultrasound waves at different angles, it is necessary to increase the number of array elements on the ultrasound probe that emit ultrasound waves. However, since there is an upper limit on the number of system channels supported by the ultrasound imaging system, when the number of ultrasound probe array elements exceeds the number of ultrasound system channels, not all ultrasound array elements can be used to emit ultrasound waves. Therefore, the scanning area, especially the scanning area with multiple angles overlapping, will be much smaller than when all array elements are emitted, thereby causing the imaging area to become smaller, affecting clinical research and diagnosis.

[0065] Exemplarily, a method for imaging blood flow velocity vector is described below, wherein Figure 1 A scanning scene of an ultrasound probe 100 is shown in FIG. 1 , wherein the ultrasound probe 100 is provided with a plurality of array elements, which are also called transducers and are important components for transmitting ultrasound waves by the ultrasound probe 100. The array elements are arranged in a certain order on the ultrasound probe 100, so the array elements on the ultrasound probe 100 can be numbered. Figure 1 As shown, the numbers on the upper side of the ultrasound probe 100 represent the numbers of the array elements. For example, the number 1 represents the first array element on the ultrasound probe 100 (i.e., the array element numbered "1"). Figure 1The ultrasonic probe 100 shown has a total of 256 array elements, so the last array element on the ultrasonic probe 100 is numbered 256. In the ultrasonic imaging device, a front-end transceiver circuit is used to drive the ultrasonic probe to transmit ultrasonic waves, wherein the front-end transceiver circuit has M transceiver channels, where M is a positive integer. Each channel in the front-end transceiver circuit is used to drive an array element on the ultrasonic probe 100. However, in some cases, the transceiver channels of the front-end transceiver circuit do not correspond one-to-one to the array elements on the ultrasonic probe 100, and there may be a situation where the number of transceiver channels of the front-end transceiver circuit is less than the number of array elements in the ultrasonic probe 100, for example Figure 1 The ultrasonic probe 100 shown has a total of 256 array elements, but the front-end transceiver circuit has only 192 transceiver channels.

[0066] When performing blood flow velocity vector imaging, it is necessary to use an ultrasonic probe 100 to transmit ultrasonic waves to a target area in multiple transmission directions, so as to obtain blood flow velocity components in different transmission directions, and to obtain blood flow velocity vector data of the target area by reconstructing these blood flow velocity components. When each array element is excited at the same time, the ultrasonic wave emitted by the ultrasonic probe 100 is perpendicular to the surface of the ultrasonic probe 100 (that is, the emission direction is the normal direction of the plane where the ultrasonic probe array element is located, or the angle between the emission direction of the ultrasonic wave and the normal is 0 degrees). If the emission direction of the ultrasonic wave is to be changed, it is only necessary to delay the emission excitation, that is, the excitation time of adjacent array elements on the ultrasonic probe 100 has a certain interval, so as to achieve the deflection of the emission angle of the ultrasonic wave.

[0067] Since the transmission direction of ultrasound waves can be changed by only delaying different array elements on the ultrasound probe 100, it can be seen that in order to realize ultrasound waves with different transmission directions required for blood flow velocity vector imaging, the most direct approach is to keep the original transmission array elements unchanged and change the time interval of excitation of each transmission channel. It can also be understood as adjusting the time parameters of each transmission channel, or superimposing a delay function on the basis of the original transmission parameters.

[0068] That is to say, currently when blood flow velocity vector imaging is performed, ultrasonic waves at different angles are emitted while keeping the transmitting array elements on the ultrasonic probe 100 unchanged.

[0069] See also Figure 1 As shown, the ultrasonic probe 100 has 256 array elements, while the front-end transceiver circuit has 192 transceiver channels, that is, the front-end transceiver circuit cannot use all the array elements on the ultrasonic probe 100 to transmit ultrasonic waves. For ease of control, array elements distributed in the middle of the ultrasonic probe 100 are usually selected as the ultrasonic array element group for transmitting ultrasonic waves. For example, Figure 1The array elements No. 33 to No. 224 are shown as an ultrasonic array element group. The array elements No. 33 and No. 224 are the boundaries of the emitted ultrasonic waves. Figure 1 In the figure, the area between the two arrows ① indicates the coverage of the first emitting direction of the ultrasonic wave, the area between the two arrows ② indicates the coverage of the second emitting direction of the ultrasonic wave, and the area between the two arrows ③ indicates the coverage of the third emitting direction of the ultrasonic wave. Figure 1 The same ultrasound array element group is used for the three ultrasound waves with different emission directions. By receiving and processing the echoes of the ultrasound waves with three different emission directions, the blood flow velocity components with three different emission directions can be obtained, and then the blood flow velocity vector can be calculated. Figure 1 The blood flow velocity vector is imaged using ultrasound waves with three different emission directions. Figure 1 Only the area covered by ultrasound waves of three different emission directions can reconstruct the blood flow velocity vector through the blood flow velocity components of three different emission directions. Therefore, the region of interest 20 (ROI) in ultrasound detection can only be set in the detection area 30 covered by ultrasound waves of three different emission directions. The range covered by blood flow velocity vector imaging is relatively small and cannot meet the current needs of clinical research and diagnosis.

[0070] In order to expand the ROI area, the best approach is to increase the number of array elements in the ultrasound array element group, for example, see Figure 2 As shown, all array elements on the ultrasonic probe 100 are used to transmit ultrasonic waves, which can increase the detection area 30 and set a larger region of interest 20. However, there is an upper limit to the number of system channels supported by the ultrasonic imaging system, and it does not support such a large number of transceiver channels. In addition, if the number of transceiver channels of the front-end transceiver circuit is to be increased, not only does it need to replace the old equipment, which causes waste, but it also needs to redesign and develop the ultrasonic imaging system, which is very costly.

[0071] Based on this, the embodiments of the present application provide a blood flow velocity vector imaging method, an ultrasound imaging method and an ultrasound imaging device, which can expand the coverage of blood flow velocity vector imaging without achieving full array element transmission and without increasing the transceiver channel data of the front-end transceiver circuit.

[0072] Figure 3 1 is a schematic diagram of the structure of an ultrasonic imaging device in an embodiment of the present application. The ultrasonic imaging device 10 may include an ultrasonic probe 100, a transmitting circuit 101, a transmitting / receiving selection switch 102, a receiving circuit 103, a beamforming circuit 104, a processor 105, a display 106 and a memory 107.

[0073] The ultrasonic probe 100 includes a transducer (not shown in the figure) composed of a plurality of array elements arranged in an array. The plurality of array elements are arranged in a row to form a linear array, or arranged in a two-dimensional matrix or other shapes to form a planar array. The plurality of array elements can also form a convex array. The arrangement of the array elements is not limited here. The array elements are used to transmit ultrasonic beams according to the excitation electrical signals, or to convert the received ultrasonic beams into electrical signals. Therefore, each array element can be used to realize the mutual conversion between the electrical pulse signal and the ultrasonic beam, so as to realize the transmission of ultrasonic waves to the target area of ​​human tissue (such as the target area in this embodiment), and can also be used to receive the echo of the ultrasonic waves reflected back by the tissue. When performing ultrasonic detection, the transmission / reception selection switch 102 can be used to control which array elements are used to transmit ultrasonic beams and which array elements are used to receive ultrasonic beams, or control the array elements to transmit ultrasonic beams or receive the echo of ultrasonic beams in time slots. The array elements participating in ultrasonic emission can be excited by electrical signals at the same time, thereby transmitting ultrasonic waves at the same time; or the array elements participating in ultrasonic emission can also be excited by several electrical signals with a certain time interval, thereby continuously transmitting ultrasonic waves with a certain time interval.

[0074] The transmitting circuit 101 is used to generate a transmission sequence according to the control of the processor 105, and the transmission sequence is used to control some or all of the multiple array elements to transmit ultrasonic waves to biological tissues, wherein the transmitting circuit 101 includes multiple transmission channels, one of which corresponds to an array element on the ultrasonic probe 100, and the transmission sequence parameters include the array element position, the number of array elements and the ultrasonic beam transmission parameters (such as amplitude, frequency, number of transmissions, transmission interval, transmission angle, waveform, focus position, etc.) used for transmission. In some cases, the transmitting circuit 101 is also used to phase delay the transmitted beam so that different transmitting array elements transmit ultrasonic waves at different times, so that each transmitted ultrasonic beam can be focused on a predetermined area of ​​interest or change the transmission direction of the ultrasonic wave. In some cases, the transmission sequence parameters of the transmitting circuit 101 can be adjusted to achieve different required ultrasonic transmission signal modulations such as dynamic focusing, delayed superposition, and apodization of the ultrasonic transmission signal. Different working modes, such as B image mode, C image mode and D image mode (Doppler mode), may have different transmission sequence parameters. After the echo signal is received by the receiving circuit 320 and processed by subsequent modules and corresponding algorithms, a B image reflecting the tissue anatomical structure, a C image reflecting the tissue anatomical structure and blood flow information, and a D image reflecting the Doppler spectrum image can be generated.

[0075] The receiving circuit 103 is used to receive the electrical signal of the ultrasonic echo from the ultrasonic probe 100 and process the electrical signal of the ultrasonic echo. The receiving circuit 103 includes multiple receiving channels, one of which corresponds to an array element on the ultrasonic probe 100. The receiving circuit 103 may include one or more amplifiers, analog-to-digital converters (ADCs), etc. The amplifier is used to amplify the electrical signal of the received ultrasonic echo after appropriate gain compensation, and the analog-to-digital converter is used to sample the analog echo signal at a predetermined time interval, thereby converting it into a digitized signal. The digitized echo signal still retains amplitude information, frequency information, and phase information. The data output by the receiving circuit 103 can be output to the beamforming circuit 104 for processing, or output to the memory 107 for storage.

[0076] The beam synthesis circuit 104 is connected to the receiving circuit 103 signal, and is used to perform beam synthesis processing such as corresponding delay and weighted summation on the signal output by the receiving circuit 103. Since the distances from the ultrasonic receiving point in the measured tissue to the receiving array element are different, the channel data of the same receiving point output by different receiving array elements have delay differences, and delay processing is required to align the phases, and weighted summation is performed on the different channel data of the same receiving point to obtain the ultrasonic image data after beam synthesis. The ultrasonic image data output by the beam synthesis circuit 104 is also called radio frequency data (RF data). In some cases, the beam synthesis circuit 104 can also synthesize different ultrasonic receiving signals according to different needs through dynamic focusing, delay superposition, and apodization to obtain ultrasonic data after beam synthesis (such as blood flow velocity vector data). The beam synthesis circuit 104 outputs the RF data to the IQ demodulation circuit. In some embodiments, the beam synthesis circuit 104 can also output the RF data to the memory 107 for caching or storage, or directly output the RF data to the image processing module of the processor 105 for image processing.

[0077] The beamforming circuit 104 may perform the above functions in the form of hardware, firmware or software. For example, the beamforming circuit 104 may include a central controller circuit (CPU), one or more microprocessor chips or any other electronic components capable of processing input data according to specific logic instructions. When the beamforming circuit 104 is implemented in software, it may execute instructions stored in a tangible and non-transitory computer-readable medium (e.g., memory 107) to perform beamforming calculations using any appropriate beamforming method.

[0078] The processor 105 is configured to be a central control circuit (CPU), one or more microprocessors, a graphics controller circuit (GPU) or any other electronic component that can process input data according to specific logical instructions. It can control peripheral electronic components according to input instructions or predetermined instructions, or read and / or save data from the memory 107. It can also process the input data by executing the program in the memory 107, for example, performing one or more processing operations on the collected ultrasound data according to one or more working modes. The processing operations include but are not limited to adjusting or limiting the form of ultrasound waves emitted by the ultrasound probe 100, generating various image frames for display on the display 106 of the subsequent human-computer interaction device, or adjusting or limiting the content and form displayed on the display 106, or adjusting one or more image display settings displayed on the display 106 (such as ultrasound images, interface components, and positioning areas of interest).

[0079] The signal processing module of the processor 105 is used to process the data output by the beamforming circuit 104 or the data output by the IQ demodulation circuit to obtain ultrasonic detection data. In one embodiment, the power spectrum of the Doppler signal changing with time can be obtained by performing spectrum analysis processing, wherein the spectrum analysis here can be implemented by using spectrum algorithms such as short-time Fourier transform (STFT) or fast Fourier transform (FFT). In another embodiment, the velocity vector of the measurement point can be output after filtering, heterodyne demodulation, autocorrelation processing and other operations.

[0080] The image processing module of the processor 105 is used to process the data output by the beamforming circuit 104 or the data output by the IQ demodulation circuit to generate a grayscale image of the signal strength change within the scanning range, which reflects the anatomical structure inside the tissue, called a B image. The image processing module can output the B image to the display 106 of the human-computer interaction device for display. The human-computer interaction device is used for human-computer interaction, that is, receiving the user's input and outputting visual information; it can receive the user's input using a keyboard, an operation button, a mouse, a trackball, etc., or a touch screen integrated with the display; it outputs the visual information using the display 106. In some cases, the image processing module of the processor 105 can further process the ultrasonic detection data output by the signal processing module to form image data for display. For example, in one embodiment, the image processing module of the processor 105 performs display processing on the power spectrum data output by the signal processing module to realize the display of the spectrum image and the spectrum envelope and spectrum measurement information on the display. In another embodiment, the image processing module of the processor 105 performs image processing on the blood flow velocity vector data output by the signal processing module to generate a blood flow motion velocity curve spectrum and display it on the display.

[0081] The blood flow velocity vector mentioned above has a velocity magnitude that is the actual velocity magnitude of the blood flow (such as red blood cells in the blood flow), or is closer to the actual velocity magnitude of the blood flow (such as red blood cells in the blood flow); its velocity direction is the actual flow direction of the blood flow (such as red blood cells in the blood flow), or is closer to the actual flow direction of the blood flow (such as red blood cells in the blood flow); the direction of the blood flow velocity vector can be in the range of 0° to 360° in the imaging plane, and its direction can represent the actual flow direction of the blood flow in the two-dimensional imaging plane.

[0082] Exemplarily, the processor 105 can also obtain an ultrasonic echo signal based on the ultrasonic echo; and obtain an ultrasonic image of the target position according to the ultrasonic echo signal. The ultrasonic image can be an ultrasonic grayscale image (referred to as B image) representing blood vessels or other tissue structures, or it can be a color ultrasonic Doppler blood flow image (referred to as color ultrasound Color image) representing blood flow information. The signal processing method for the ultrasonic echo signal includes but is not limited to beamforming, orthogonal demodulation, wall filtering, color coding, etc. of the ultrasonic echo signal. The ultrasonic image obtained by the processor 105 can be stored in the memory 107. And the ultrasonic image can be displayed on the display 106. Among them, the wall filtering step of the traditional color ultrasound processing can use traditional IIR or FIR filters to obtain a blood flow signal with a high signal-to-noise ratio, and then process the blood flow signal to calculate the blood flow velocity.

[0083] The memory 107 may be a tangible and non-transitory computer-readable medium, such as a flash memory card, a solid-state memory, a hard disk, etc., for storing data or programs. For example, the memory 107 may be used to store acquired ultrasound data or image frames generated by the processor 105 that are not immediately displayed, or the memory 107 may store a graphical user interface, one or more default image display settings, or programming instructions for a processor, a beamforming circuit, or an IQ demodulation circuit.

[0084] It should be noted that Figure 3 The structure is only for illustration and may also include Figure 3 More or fewer components as shown, or with Figure 3 Different configurations are shown. Figure 3 Each component shown in the figure may be implemented by hardware and / or software.

[0085] In one embodiment of the present application, the display 106 of the aforementioned ultrasonic imaging device 10 may be a touch screen, a liquid crystal display, etc., or it may be an independent display device such as a liquid crystal display, a television, etc. that is independent of the ultrasonic imaging device 10, or it may be a display screen on electronic devices such as mobile phones and tablet computers, etc.

[0086] In one embodiment of the present application, the memory 107 of the aforementioned ultrasonic imaging device 10 may be a flash memory card, a solid-state memory, a hard disk, etc. In one embodiment of the present application, a computer-readable storage medium is also provided, which stores a plurality of program instructions, and after the plurality of program instructions are called and executed by the processor 105, some steps or all steps or any combination of steps in the blood flow velocity processing method in each embodiment of the present application may be executed. In one embodiment, the computer-readable storage medium may be the memory 107, which may be a non-volatile storage medium such as a flash memory card, a solid-state memory, a hard disk, etc.

[0087] In one embodiment of the present application, the processor 105 of the aforementioned ultrasound imaging device 10 can be implemented by software, hardware, firmware or a combination thereof, and can use circuits, single or multiple application-specific integrated circuits (ASICs), single or multiple general-purpose integrated circuits, single or multiple microprocessors, single or multiple programmable logic devices, or a combination of the aforementioned circuits or devices, or other suitable circuits or devices, so that the processor 105 can execute the corresponding steps of the blood flow velocity processing method in each embodiment of the present application.

[0088] Combination Figure 3 The schematic structural block diagram of the ultrasonic imaging device 10 shown in FIG. Figure 4The blood flow velocity vector imaging method provided by an embodiment of the present application may include but is not limited to the following steps 410 to 460:

[0089] Step 410: Control at least two groups of ultrasound array elements on the ultrasound probe through the front-end transceiver circuit to transmit non-focused ultrasound waves to the target area in different transmission directions.

[0090] In this step, the front-end transceiver circuit includes a transmitting circuit 101, and the processor 105 controls the transmitting circuit 101 to sequentially transmit ultrasound waves in different transmitting directions. In one embodiment, the processor 105 controls the ultrasound imaging device 10 to be in an ultrasound transmitting state or an ultrasound receiving state through the transmitting / receiving selection switch 102, and the number of transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasound probe 100, that is, the number of transmitting channels of the transmitting circuit 101 is less than the number of all array elements distributed on the ultrasound probe 100.

[0091] In this step, each group of ultrasound array elements includes a plurality of array elements distributed on the ultrasound probe that are less than or equal to the number of all the transmitting and receiving channels, and each group of ultrasound array elements has a plurality of array elements at the same position and at least one array element at a different position distributed on the ultrasound probe. One group of ultrasound array elements corresponds to one emission direction, and the angle between the emission direction of the unfocused ultrasound and the normal direction of the plane where the array element of the ultrasound probe is located is less than or equal to 45 degrees.

[0092] In another embodiment, the positions of the array elements included in at least two groups of ultrasound array elements on the ultrasound probe are completely different, that is, the positions of the ultrasound array elements of at least two groups on the ultrasound probe 100 have no overlapping parts.

[0093] In one embodiment, see Figure 5a The scanning scene of an ultrasound probe 100 is shown, and two groups of ultrasound array elements are arranged on the ultrasound probe 100, including a first ultrasound array element group 501 and a second ultrasound array element group 502. The first ultrasound array element group 501 and the second ultrasound array element group 502 each include 192 array elements, and the array elements of the first ultrasound array element group 501 are numbered from 65 to 256 on the ultrasound probe 100. The array elements of the second ultrasound array element group 502 are numbered from 1 to 192 on the ultrasound probe 100. It can be seen that the first ultrasound array element group 501 and the second ultrasound array element group 502 have the same number of array elements in the first ultrasound array element group 501, see Figure 5a As shown, the array elements numbered 65 to 192 are the array elements with the same position shared by the first ultrasonic array element group 501 and the second ultrasonic array element group 502, and the array elements numbered 1 to 64 in the first ultrasonic array element group 501 and the array elements numbered 193 to 256 in the second ultrasonic array element group 502 are array elements in different positions. Figure 5aIn the illustrated embodiment, each ultrasound array element group has the same number of array elements. In practice, the number of array elements in different ultrasound array element groups may be different.

[0094] The first ultrasound array element group 501 transmits non-focused ultrasound in a first direction. Figure 5a In FIG. 5 , the area between the two arrows ① is the coverage range of the ultrasound wave emitted by the first ultrasound array element group 501, and the direction indicated by the arrow ① is the first direction. Correspondingly, the second ultrasound array element group 502 emits non-focused ultrasound wave in the second direction. Figure 5a In FIG. 5 , the area between the two arrows ② is the coverage range of the ultrasound wave emitted by the second ultrasound array element group 502, and the direction indicated by the arrow ② is the second direction. It can be seen that the first target area 510 covered by the ultrasound waves emitted by the first ultrasound array element group 501 and the second ultrasound array element group 502 is the detection area of ​​the blood flow velocity vector data.

[0095] For comparison, see Figure 5b As shown, if the ultrasound probe 100 is only provided with the first target ultrasound array element group 500, and the number of array elements of the first target ultrasound array element group 500 is also 192, ultrasound waves are also emitted in the first emission direction indicated by arrow ① and the second emission direction indicated by arrow ②, and the second target area 520 covered by the two ultrasound waves is the detection area of ​​the blood flow velocity vector data. Figure 5b and Figure 5a By comparison, Figure 5a The area of ​​the first target area 510 is larger than Figure 5b The second target area 520 in the image is larger.

[0096] Figure 5a Two types of ultrasonic array element groups are shown in FIG. 1 . In practice, more ultrasonic array element groups may be provided. For example, see Figure 5c As shown, the ultrasonic probe 100 is provided with three groups of ultrasonic array elements. Figure 5a A third ultrasonic array element group 503 is added on the basis of Figure 5c As shown, the direction in which the third ultrasonic array element group 503 transmits ultrasonic waves is the third transmitting direction ( Figure 5c The area between the two arrows ③ is the coverage of the ultrasonic wave emitted by the third ultrasonic array element group 503. In one embodiment, the third emission direction is perpendicular to the plane where the ultrasonic probe is located, the angles between the first emission direction and the second emission direction and the third emission direction are greater than 0 degrees and less than or equal to 45 degrees, and the first emission direction and the second emission direction are respectively deviated from the left and right sides of the third emission direction.

[0097] In one embodiment of step 410, the ultrasonic waves emitted by each group of ultrasonic array elements are non-focused ultrasonic waves, for example, Figure 5a and Figure 5cAs shown, the ultrasound array element group emits a plane wave. In another embodiment, the non-focused ultrasound wave emitted by the ultrasound array element group may also be a divergent wave. Since the non-focused wave is used in this step to measure the blood flow velocity vector at the target position of the target area of ​​the target object, a higher sampling frame rate is provided. In one embodiment, the maximum imaging frame rate of the blood flow velocity vector imaging is greater than 100 Hz.

[0098] In one embodiment, the number of array elements of the ultrasonic array element group corresponds to the number of all transceiver channels of the front-end transceiver circuit. For example, if the number of all transceiver channels of the front-end transceiver circuit is 192, the number of array elements of the ultrasonic array element group is at most 192. Of course, the number of all transceiver channels of the front-end transceiver circuit is related to the hardware and performance of the ultrasonic imaging device 10. In one embodiment, the number of all transceiver channels of the front-end transceiver circuit is greater than or equal to 96 and less than or equal to 192.

[0099] Step 420, controlling the ultrasonic probe to receive the echo of the unfocused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the unfocused ultrasonic wave corresponding to different transmission directions.

[0100] In this step, the target area returns the corresponding ultrasonic echo after receiving the ultrasonic wave emitted by the ultrasonic probe 100, wherein ultrasonic waves in different emission directions correspond to different ultrasonic echoes, and the ultrasonic echoes returned by the target area are received by the ultrasonic probe 100 and sent to the receiving circuit 103 for conversion into echo signals. Among them, the echoes received by the ultrasonic probe 100 correspond to the ultrasonic waves emitted in different emission directions in step 410. For example, if two ultrasonic waves in different emission directions are emitted in step 410, then in this step, echoes in two different emission directions will be received accordingly, and two echo signals corresponding to different emission directions will be obtained.

[0101] In one embodiment, the ultrasonic probe 100 acquires echo signals of different transmission directions in a sequential manner. For example, after controlling the first ultrasonic array element group 501 to transmit an unfocused ultrasonic wave in a first direction, the processor 105 controls the transmit / receive selection switch 102 to be in a receiving state to receive the echo of the ultrasonic wave in the first transmission direction. Then, after controlling the second ultrasonic array element group 502 to transmit the next unfocused ultrasonic wave in a second direction, the processor 105 controls the transmit / receive selection switch 102 to be in a receiving state to receive the echo of the ultrasonic wave in the second transmission direction, thereby obtaining the echo signals of the ultrasonic waves in the first transmission direction and the second transmission direction. In another embodiment, the processor 105 controls the first ultrasonic array element group 501 and the second ultrasonic array element group 502 to transmit an unfocused ultrasonic wave to the target area in sequence, and controls the transmit / receive selection switch 102 to be in a receiving state to receive the echo of the ultrasonic wave in the first transmission direction and the echo of the ultrasonic wave in the second transmission direction in sequence.

[0102] In this step, the ultrasonic probe 100 can be used to obtain multiple echoes of unfocused ultrasonic waves in the same transmission direction, for example, the unfocused ultrasonic waves transmitted by the first ultrasonic array element group 501 to the first transmission direction at time t1, and the unfocused ultrasonic waves transmitted by the first ultrasonic array element group 501 to the first transmission direction at time t2, and these unfocused ultrasonic waves transmitted by the same ultrasonic array element group and the same transmission direction but at different times can be classified as a group of unfocused ultrasonic echo signals, that is, one transmission direction corresponds to a group of unfocused ultrasonic echoes, and a group of unfocused ultrasonic echo signals includes unfocused ultrasonic waves transmitted at least twice in one transmission direction. After the unfocused ultrasonic echoes obtained by the ultrasonic probe 100 are processed by the receiving circuit 103, at least two groups of unfocused ultrasonic echo signals corresponding to different transmission directions can be obtained. For example, if there are three ultrasonic array element groups, three groups of unfocused ultrasonic echo signals can be obtained.

[0103] Step 430: Obtain at least two blood flow velocity components corresponding to different emission directions according to at least two groups of unfocused ultrasonic echo signals.

[0104] In this step, the processor 105 calculates the blood flow velocity for each group of non-focused ultrasonic echo signals of different transmission directions obtained by the receiving circuit 103, and obtains the blood flow velocity components of different transmission directions corresponding to each target position in the target area, wherein one transmission direction corresponds to one blood flow velocity component. In one embodiment, since the frequency shift of the target point in the target area can reflect the blood flow velocity, the blood flow velocity can be calculated based on the echo signals of non-focused ultrasonic waves transmitted in the same transmission direction but at different times, and the receiving time interval of these echo signals (or the transmission time interval of non-focused ultrasonic waves in the same transmission direction) to obtain the blood flow velocity component in the current transmission direction. In addition, since at least two blood flow velocity components are required to calculate the blood flow velocity vector in the subsequent steps, it is necessary to obtain at least two groups of non-focused ultrasonic echo signals, and calculate the blood flow velocity components in the corresponding transmission directions respectively.

[0105] For example, by calculating the echoes of a group of unfocused ultrasonic waves emitted by the first ultrasonic array element group 501, a first blood flow velocity component in the first emission direction is obtained. Similarly, by calculating the echoes of a group of unfocused ultrasonic waves emitted by the second ultrasonic array element group 502, a second blood flow velocity component in the second emission direction is obtained.

[0106] In one embodiment, a blood flow velocity component in a transmission direction may be calculated based on a group of non-focused ultrasonic echoes. For example, for a certain transmission direction, multiple ultrasonic echoes in a certain transmission direction may be received, and then the blood flow velocity component in a transmission direction may be calculated based on ultrasonic echoes received at different time intervals in the same transmission direction.

[0107] In one embodiment, the blood flow velocity component in one emission direction can be calculated by an autocorrelation method:

[0108]

[0109]

[0110] Among them, v z represents the velocity component calculated under different emission directions, f0 represents the center frequency of the probe emission signal, T prf is the time interval between two transmissions at the same angle, N represents the number of transmissions, x(i) represents the real part of the signal after the i-th transmission and reception, and y(i) represents the imaginary part of the signal after the i-th transmission and reception. is the imaginary part operator, is the real part operator, and j is the imaginary unit.

[0111] Step 440, reconstructing the velocity of at least two blood flow velocity components in different emission directions to obtain blood flow velocity vector data of the target area.

[0112] In this step, the processor 105 reconstructs the blood flow velocity vectors in different emission directions to obtain the blood flow velocity vector data of the target area. Wherein, a blood flow velocity vector represents a velocity vector of a target position in the target area, and multiple target positions can be set in the target area, and the blood flow velocity vectors of multiple target positions in the target area constitute the blood flow velocity vector data of the target area.

[0113] In this step, the blood flow velocity vector of a target position can be reconstructed by the blood flow velocity components of different emission directions of the target position. The following takes the reconstruction of blood flow velocity components of three different emission directions as an example, see Figure 6 As shown, the velocity component of the blood flow velocity vector at the target position in the first emission direction is the first blood flow velocity v1, the velocity component of the blood flow velocity vector at the target position in the second emission direction is the second blood flow velocity v2, and the velocity component of the blood flow velocity vector at the target position in the second emission direction is the second blood flow velocity v3. Through velocity reconstruction, vertical lines are drawn for the velocity components in three different emission directions, and the first velocity vector at the target position can be determined according to the intersection of the three vertical lines. The above reconstruction of the velocity components corresponding to the three different emission directions is only a schematic illustration. For the reconstruction of the velocity components corresponding to different emission directions, please refer to Figure 6The present application does not limit the number of velocity components, and for velocity reconstruction of velocity components corresponding to two or more than three emission directions, the above-mentioned relevant descriptions can also be referred to for understanding, and are not exhaustive here.

[0114] Step 450: obtaining a blood flow velocity vector image of the target area based on the blood flow velocity vector data of the target area.

[0115] In this step, the processor 105 performs image processing on the blood flow velocity vector data of the target area to obtain a blood flow velocity vector image of the target area. In one embodiment, the blood flow velocity vector image includes blood flow velocity vector markers for each target position of the target area, that is, the blood flow velocity vector is represented by a dynamic or static marker on the ultrasound image, wherein the direction of the marker represents the velocity direction of the blood flow velocity vector, and the size or transparency of the marker represents the velocity magnitude of the blood flow velocity vector. The blood flow velocity vector is represented by a dynamic marker on the ultrasound image, including: the position of the marker on two adjacent frames of ultrasound images is dynamically updated to form a flow-like effect that changes with time, wherein the position of the marker represents the corresponding position of the blood flow in the vascular tissue.

[0116] In one embodiment, it should be noted that the dynamic display of the blood flow velocity vector image can be presented by displaying dynamic markers on the ultrasound image. The specific implementation can refer to the following description: First, the size and direction of the blood flow velocity vector of the current frame blood flow is obtained, and then some markers are randomly displayed in the ultrasound image of the vascular tissue. Among them, these markers can be symbols such as arrows, triangles, circles, etc. According to the size and direction of the blood flow velocity vector corresponding to the position of each marker in the current frame, combined with the time interval between two adjacent frames, the position of the marker in the next frame is calculated, and then the marker is displayed. Similarly, when several frames of images are displayed together, the flow effect of blood flow can be visually presented.

[0117] Step 460: Display the blood flow velocity vector image.

[0118] In this step, the processor 105 displays the blood flow velocity vector image obtained after the above step 450 through the display 106. It can be a static blood flow velocity vector image or a dynamic blood flow velocity vector image (i.e., a video image showing a blood flow effect).

[0119] In the blood flow velocity vector imaging method provided by the embodiment of the present application, the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe, and the front-end transceiver circuit controls at least two groups of ultrasonic array elements on the ultrasonic probe to transmit non-focused ultrasonic waves to the target area in different transmission directions respectively, and the front-end transceiver circuit controls the ultrasonic probe to receive the echo of the non-focused ultrasonic waves returned by the target area, and obtains the echo signals of the non-focused ultrasonic waves corresponding to the different transmission directions respectively, and obtains the blood flow velocity components corresponding to the different transmission directions according to the echo signals of the non-focused ultrasonic waves in the different transmission directions and reconstructs these blood flow velocity components to obtain the blood flow velocity vector of the target area. Wherein, each group of ultrasonic array elements includes a plurality of array elements distributed on the ultrasonic probe that are less than or equal to the number of all transceiver channels, and each group of ultrasonic array elements has a plurality of array elements at the same position and at least one array element at a different position distributed on the ultrasonic probe. Compared with using the same ultrasound array element group to transmit ultrasound waves at different angles for blood flow velocity vector detection, in the embodiment of the present application, since the array elements of the ultrasound array element group corresponding to different emission directions are distributed at positions staggered on the ultrasound probe, it is possible to increase the overlapping range of non-focused ultrasound waves emitted by each of the ultrasound array element groups in different emission directions without increasing the number of array elements of the ultrasound array element group and the number of transceiver channels, thereby improving the coverage range of blood flow velocity vector imaging.

[0120] In one embodiment, the positions of each ultrasonic array element group on the ultrasonic probe 100 may be allocated by the following method. The distribution of an ultrasonic array element group on the ultrasonic probe 100 may be numbered by the position of the first array element and the position of the last array element. For example, for the first group of ultrasonic array elements in the first transmission direction, there may be:

[0121] E1=1;E 1L =L,

[0122] Wherein, E1 represents the number of the first array element of the first group of ultrasonic array elements, and E1=1 represents that the first array element of the first group of ultrasonic array elements is the array element numbered 1 on the ultrasonic probe 100. When the length of the first group of ultrasonic array elements is known to be L, it can be obtained that the number of the last array element of the first group of ultrasonic array elements is L, and E1 is used to represent the first array element numbered L. 1L =L. We can use {E1=1; E 1L =L} represents the array element distribution of the first group of ultrasonic array elements.

[0123] For the second group of ultrasonic array elements, its array element distribution can be expressed as:

[0124] E 2L =L+E2-1;

[0125] Among them, E2 and E 2L represents the first array element and the last array element of the second group of ultrasound array elements, wherein K represents the total number of array elements on the ultrasound probe 100, and N represents the number of different transmission directions used in blood flow velocity vector imaging, wherein K and N are both positive integers.

[0126] Similarly, for the third group of ultrasonic array elements, its array element distribution can be expressed as:

[0127] E 3L =L+E3-1;

[0128] The array element distribution of the i-th group of ultrasonic array elements can be expressed as:

[0129] E iL =L+E i -1; where i is a positive integer, 0≤i≤N;

[0130] Similarly, the array element distribution of the Nth group of ultrasonic array elements can be expressed as:

[0131] E NL =L+E N -1.

[0132] In the above embodiment, the number of array elements in the ultrasound array element group is equal to the maximum number of transceiver channels supported by the front-end transceiver circuit. This can improve the performance of blood flow velocity vector imaging of the target area in the ultrasound imaging device 10 as much as possible. i When the value of is a non-integer, it can be rounded up or down or rounded off. In addition, in some embodiments, the number of ultrasonic array element groups can also be less than the maximum number of transceiver channels supported by the front-end transceiver circuit. In the above-mentioned method of allocating ultrasonic array element groups, the scanning area is symmetrical relative to the center of the array element ultrasonic probe 100, so the ROI area is preferably set at the position of the central axis of the ultrasonic probe 100.

[0133] In one embodiment, the processor 105 may control each ultrasound array element group on the ultrasound probe 100 to repeatedly transmit non-focused ultrasound waves in sequence in a transmission direction that is preset or calculated according to other conditions (described in detail below), for example, Figure 7As shown, arrow ① indicates the unfocused ultrasonic wave emitted by the first ultrasonic array element group 501 in the first emission direction, arrow ② indicates the unfocused ultrasonic wave emitted by the second ultrasonic array element group 502 in the second emission direction, and arrow ③ indicates the unfocused ultrasonic wave emitted by the third ultrasonic array element group 503 in the third emission direction. It can be seen that the first ultrasonic array element group 501, the third ultrasonic array element group 503 and the second ultrasonic array element group 502 emit unfocused ultrasonic waves in turn in the first emission direction, the third emission direction and the second emission direction respectively.

[0134] Based on the above-mentioned embodiments, the blood flow velocity vector at the target position can be detected within the coverage range of the ultrasound waves emitted by different ultrasound array element groups. Therefore, in one embodiment, the positions of different ultrasound array element groups on the ultrasound probe 100 and the emission directions of ultrasound waves of different ultrasound array element groups can be fixed, so that the measurement range of the blood flow velocity vector in the target area can be fixed. Of course, different working modes can also be set. In different working modes, the emission direction of ultrasound waves emitted by the ultrasound array element group and / or the position of the ultrasound array element group on the ultrasound probe 100 are different. In addition, before or during the ultrasound array element group emitting ultrasound waves, the controller 105 can control the display 106, and the display 106 displays the following information: Figure 5a The first target area 510 is used to indicate the ultrasonic examination range. In one embodiment, the user can set a region of interest (ROI area) within the coverage of the ultrasonic waves emitted by different ultrasonic array element groups, and use the region of interest to further perform blood flow velocity vector measurement.

[0135] In one embodiment, in addition to fixing or presetting (user setting, working mode setting, etc.) the position and transmission direction of the ultrasonic array element group, the transmission direction of the ultrasonic array element group transmitting the ultrasonic wave and / or the position of the ultrasonic array element group on the ultrasonic probe 100 can be dynamically changed according to the target condition. The target condition can be the detection result of the ultrasonic imaging device 10 or the intermediate detection parameter of the measurement process, or other user-configured measurement parameters other than directly setting the transmission direction and / or the position of the ultrasonic array element group, for example, dynamically adjusting the transmission direction of the ultrasonic array element group transmitting the ultrasonic wave and / or the position of the ultrasonic array element group on the ultrasonic probe 100 according to the ROI area set by the user.

[0136] In one embodiment, step 410 in the above embodiment specifically includes the following steps 411 to 412:

[0137] Step 411, obtaining a region of interest of the target area.

[0138] In this step, the user can set the region of interest through a human-computer interaction device (not shown in the figure) provided in the ultrasonic imaging device 10, wherein the human-computer interaction device is used for human-computer interaction, that is, receiving user input and outputting visual information; it can receive user input by using a keyboard, operation button, mouse, trackball, etc., or a touch screen integrated with a display; it outputs visual information by using the display 106. For example, the ultrasonic imaging device 10 performs ultrasonic imaging on the target area, and displays a B image through the display 106, and then the user can set the ROI region in the B image displayed on the display 106 through the human-computer interaction device.

[0139] Step 412: According to the region of interest, at least two groups of ultrasound array elements on the ultrasound probe are controlled by the front-end transceiver circuit to transmit unfocused ultrasound waves to the target region in different transmission directions, wherein the unfocused ultrasound waves transmitted by different ultrasound array element groups all cover the region of interest.

[0140] In this step, the processor 105 controls the transmitting circuit 101 to drive different ultrasound array element groups to transmit unfocused ultrasound waves to the ROI area in different transmitting directions in turn. For details on how different ultrasound array element groups transmit unfocused ultrasound waves in different transmitting directions, please refer to the description of the above step 410 and related embodiments, which will not be repeated here.

[0141] In one embodiment, the ROI region in step 411 is obtained by following steps 610 to 630:

[0142] Step 610: Control the ultrasonic probe to send a first ultrasonic wave to the target area, receive an echo of the first ultrasonic wave returned from the target area, and obtain an echo signal of the first ultrasonic wave.

[0143] In this step, the transmitting circuit 101 is used to generate a transmission sequence according to the control of the processor 105. The transmission sequence is used to control some or all of the multiple array elements to transmit ultrasound to the target tissue. The transmission sequence parameters include the array element position, the number of array elements and the ultrasound beam transmission parameters (such as amplitude, frequency, number of transmissions, transmission interval, transmission angle, waveform, focus position, etc.) used for transmission. In some cases, the transmitting circuit 101 is also used to phase delay the transmitted beam so that different transmitting array elements transmit ultrasound at different times so that each transmitted ultrasound beam can be focused on a predetermined area of ​​interest. Different working modes, such as B image mode or C image mode, correspond to different transmission sequence parameters. Among them, the first ultrasound wave can be a plane wave, a focused wave or a divergent wave. After receiving the first ultrasound wave, the target area (such as a target tissue such as a blood vessel) returns the echo of the first ultrasound wave, so that the echo of the returned first ultrasound wave is received by the ultrasound probe 100 and sent to the receiving circuit 103 to be converted into an electrical signal, and then the beam synthesis circuit 104 performs beam synthesis processing to obtain the first ultrasound echo signal. In one embodiment, the first ultrasonic echo signal may be stored in the memory 107 to wait for further processing. In another embodiment, the first ultrasonic echo signal may be processed and displayed by an image processing module of the processor 105 .

[0144] Step 620: Obtain a tissue image of the target area according to the echo signal of the first ultrasonic wave.

[0145] In this step, the first ultrasonic echo signal output by the beamforming circuit 104 can be processed by the image processing module of the processor 105 to generate a grayscale image of the signal strength change within the scanning range, and the grayscale image reflects the tissue structure of the target tissue, such as a tissue image of a blood vessel. In one embodiment, the tissue image can be a B image or an E image that only reflects the anatomical structure inside the tissue, or a C image that reflects the anatomical structure inside the tissue and blood flow information. In one embodiment, the processor 105 can store the tissue image of the target tissue in the memory 107 for subsequent further processing. In another embodiment, the tissue image of the target tissue can also be displayed in real time by the display 106.

[0146] Step 630: display the tissue image and acquire the region of interest set in the tissue image.

[0147] In this step, the tissue image of the target tissue processed by the image processing module of the processor 105 and the identified tissue structure identified in step 230 can be displayed by the display 106. In one embodiment, the identified tissue structure set can be used as a processing unit to display the identified tissue structures in the identified tissue structure set. For example, the tissue image of the target tissue displayed by the display 106 can be a B image, a C image, an E image, or an M image. After the user sets the ROI area through the human-computer interaction device, the position (e.g., depth), boundary (e.g., shape and size) or area of ​​the ROI area set by the user will be acquired by the processor 105.

[0148] In one embodiment, the scanning range of the ultrasound probe 100, the transmission direction of the ultrasound array element group transmitting the ultrasound waves and / or the position of the ultrasound array element group on the ultrasound probe 100 can be determined according to the ROI area set by the user, so that the ultrasound waves emitted by these ultrasound array element groups can cover the ROI area set by the user.

[0149] In one embodiment, see Figure 8 As shown, the above step 412 specifically includes the following steps 810 to 820:

[0150] Step 810: determining the distribution positions of the array elements of each ultrasound array element group in the ultrasound probe on the ultrasound probe according to the boundary of the region of interest and different preset transmission directions of at least two groups of ultrasound array element groups.

[0151] In this step, the processor 105 obtains the ROI area set by the user according to the above-mentioned step 411 and its related embodiments, and determines the boundary of the ROI area according to the relevant parameters of the ROI area (such as the center position, the shape or size of the boundary, etc.), and then determines the position of each ultrasonic array element group on the ultrasonic probe (that is, the distribution position of the array elements of each ultrasonic array element group on the ultrasonic probe) according to the boundary of the ROI area and the preset transmission direction of different ultrasonic array element groups.

[0152] In one embodiment, the processor 105 obtains the preset transmission direction of the ultrasonic array element group whose position needs to be determined and the preset number of array elements of the ultrasonic array element group (which can be understood as the aperture size of the ultrasonic array element group). According to the aperture size of the ultrasonic array element group and the preset transmission direction, the area size of the ultrasonic coverage range of the array element group of the current aperture can be determined. By changing the position of the ultrasonic array element group, the determined ultrasonic coverage range can cover the ROI area. The current position of the ultrasonic array element group is the target position. There are many ways to change the position of the ultrasonic array element group so that its ultrasonic coverage range can cover the ROI area, and this application does not limit this. For example, a straight line can be determined with the center of the ROI area and the preset transmission direction. The intersection of the straight line and the ultrasonic probe 100 is the center of the ultrasonic array element group. Then, according to the aperture size of the current ultrasonic array element group, the position of the first array element of the ultrasonic array element group and the position of the last array element are determined, and the position of the ultrasonic array element group on the ultrasonic probe 100 can be determined. In one embodiment, if the ultrasound waves emitted by the ultrasound array element group at the current position cannot cover the ROI area (i.e., the area determined by the first array element, the last array element, and the preset transmission direction cannot cover the ROI area), the number of array elements in the ultrasound array element group can be increased (i.e., the number of the first array element is reduced and / or the number of the last array element is increased), and the user can be prompted to reset the ROI area (i.e., return to step 411). By presetting the number of array elements in the ultrasound array element group, the aperture sizes of ultrasound array element groups in different transmission directions can be kept consistent, thereby reducing the complexity of the control algorithm of the ultrasound probe 100.

[0153] In another embodiment, the number of array elements of the target array element group may not be preset, but the position of the ultrasound array element group is directly determined on the ultrasound probe 100 according to the boundary of the region of interest and the preset transmission direction. Instead, two boundary lines having only one intersection with the region of interest are first determined according to the preset transmission direction, and the two boundary lines are respectively located on both sides of the ROI region, and then the position of the first array element and the position of the last array element of the ultrasound array element group are determined according to the intersection of the two boundary lines and the ultrasound probe 100, and then the positions of the array elements on the current ultrasound array element group distributed on the ultrasound probe (i.e., the positions of the ultrasound array element group on the ultrasound probe 100) are determined.

[0154] The boundary of the ROI region may be in different shapes, such as a polygon, a circle, or an ellipse, wherein the polygon may also be a quadrilateral, a rectangle, a trapezoid, or the like.

[0155] In one embodiment, taking the ROI region as a polygon, the position with only one intersection with the ROI region is the vertex of the polygon. Therefore, the boundary lines on both sides of the ROI region can be determined according to the vertex of the ROI region and the preset transmission direction of the current ultrasound array element group, and then the position of the ultrasound array element group can be determined. That is, according to the vertex of the region of interest and the different preset transmission directions of at least two groups of ultrasound array element groups, the positions of the array elements of each ultrasound array element group in the ultrasound probe on the ultrasound probe are determined.

[0156] In another embodiment, taking the ROI area as a circle as an example, two tangents of the circle can be determined according to the preset transmission direction, and the position of the ultrasound array element group on the ultrasound probe can be determined by using the two tangents as boundary lines.

[0157] In one embodiment, the ROI region is a quadrilateral, and therefore, the position with only one intersection point with the ROI region is the diagonal of the quadrilateral. Therefore, the boundary lines on both sides of the ROI region can be determined according to the diagonal of the ROI region and the preset emission direction of the current ultrasound array element group, and then the position of the ultrasound array element group can be determined. According to the diagonal of the region of interest and the different preset emission directions of at least two groups of ultrasound array element groups, the positions of the array elements of each ultrasound array element group in the ultrasound probe on the ultrasound probe are determined. For example, see Figure 9a As shown, the boundary of the ROI region 910 is a quadrilateral located at Figure 9a The upper left corner and the lower right corner of the ROI region 910 shown in FIG. 9A determine the position of the ultrasound array element group on the ultrasound probe 100. For example, the preset transmission direction of the first ultrasound array element group 501 is Figure 9a According to the direction indicated by the arrow ①, the first boundary line 920 can be determined according to the direction indicated by the arrow ① and the vertex at the upper left corner of the ROI area 910. The array element number at the intersection of the first boundary line 920 and the ultrasonic probe 100 is 51. Similarly, according to the direction indicated by the arrow ① and the vertex at the lower right corner of the ROI area 910, the second boundary line 930 can be determined. The array element number at the intersection of the second boundary line 930 and the ultrasonic probe 100 is 210. Therefore, the array elements of the first ultrasonic array element group 501 are distributed on the ultrasonic probe at the array elements numbered 51 to 210. Similarly, for the second ultrasonic array element group 502, the upper left corner and the lower right corner of the ROI area can also be used to determine the third boundary line 940 and the fourth boundary line 950, and then determine that the first array element number of the second ultrasonic array element group 502 is 65, and the last array element number is 256, that is, the array elements of the second ultrasonic array element group 502 are respectively located on the ultrasonic probe 100 at the array elements numbered 65 to 256. Of course, in one embodiment, the lower left corner and the upper right corner of the ROI area 910 may also be used to determine the position of the array element of the ultrasound array element group.

[0158] Figure 9aIn the embodiment, different ultrasound array element groups use the same diagonal angle to determine the positions of the first array element and the last array element on the ultrasound probe 100. In another embodiment, different ultrasound array element groups may use different diagonals to determine the positions of the ultrasound array element groups on the ultrasound probe 100, for example, see Figure 9b As shown, the first ultrasonic array element group 501 uses the lower left corner and the upper right corner of the ROI area 910 to determine the position of the array element distribution, and the second ultrasonic array element group 502 uses the upper left corner and the lower right corner of the ROI area 910 to determine the position of the array element distribution. The positions of the first ultrasonic array element group 501 distributed on the ultrasonic probe 100 are the array elements numbered 1 to 160. The positions of the second ultrasonic array element group 502 distributed on the ultrasonic probe 100 are the array elements numbered 65 to 256.

[0159] In another embodiment, if the preset transmission direction is perpendicular to the ultrasound probe 100 (or the angle between the normal line of the plane where the array element of the ultrasound probe 100 is located is 0 degrees), the positions of the array elements of the ultrasound array element group on the ultrasound probe can be directly determined according to the projection of the region of interest on the plane where the array element of the ultrasound probe is located, wherein the ultrasound array element group includes the array elements covered by the projection of the region of interest on the plane where the array element of the ultrasound probe is located. For example, see Figure 9a and Figure 9b As shown, the third transmitting direction of the third ultrasound array element group 503 is the direction indicated by arrow ③, and the third transmitting direction is perpendicular to the plane where the ultrasound probe 100 is located. Therefore, it can be determined that the distribution range of the array elements of the third ultrasound array element group 503 is the array elements numbered 21 to 166 according to the projection of the ROI area 910 on the ultrasound probe 100.

[0160] exist Figure 9a In the embodiment, the coverage range of the ultrasonic wave emitted by the first ultrasonic array element group 501 is the area between the two arrows ①, that is, the same as the area covered between the first boundary line 920 and the second boundary line 930. When the coverage range of the emitted ultrasonic wave is close to the ROI area, the number of array elements of the ultrasonic array element group can be reduced, which can not only reduce the burden of the ultrasonic imaging device 10 and reduce energy consumption, but also reduce the temperature of the ultrasonic probe 100 when emitting ultrasonic waves, thereby improving the safety of the ultrasonic imaging device 10 and the user's comfort. However, in order to avoid the loss of measurement data at the ROI boundary position, in some embodiments, a certain margin distance can be reserved, that is, the coverage range of the ultrasonic wave emitted by the ultrasonic array element group can be appropriately expanded, for example, see Fig.9c As shown, taking the first ultrasonic array element group 501 as an example, the coverage of the two arrows ① of the first ultrasonic array element group 501 is larger than the area covered by the first boundary line 920 and the second boundary line 930. Fig.9cIn one embodiment, the position of the originally determined ultrasonic array element group can be appropriately expanded by a certain distance, for example, the number of the first array element of the ultrasonic array element group is shifted to the left (the number is reduced), and the number of the last array element is shifted to the right (the number is increased). In another embodiment, when determining the diagonal of the ROI area 910, the ROI area 910 can be expanded, that is, after increasing the area of ​​the ROI area 910, the first boundary line 920 and the second boundary line 930 are determined according to the diagonal of the ROI area 910 after the area is increased. In this way, the coverage range of the ultrasonic wave emitted by the finally determined ultrasonic array element group will be larger than Figure 9a The one in is bigger.

[0161] In one embodiment, the coverage range of each ultrasonic array element group transmitting ultrasonic waves may have a certain margin relative to the ROI area 910. In other embodiments, only the coverage range of some ultrasonic array element groups transmitting ultrasonic waves may have a margin. For example, see Figure 9d As shown in the figure, the coverage range of the ultrasonic waves transmitted by the first ultrasonic array element group 501 and the second ultrasonic array element group 502 both leave a certain margin with the ROI area 910, while the coverage range of the ultrasonic waves transmitted by the third ultrasonic array element group 503 whose transmission direction is perpendicular to the ultrasonic probe 100 is close to the ROI area 910. This is because compared with the first transmission direction and the second transmission direction, the third transmission direction perpendicular to the ROI area 910 is not prone to errors, so the number of array elements of the third ultrasonic array element group 503 can be reduced as much as possible, which can save energy consumption and reduce the surface temperature of the ultrasonic probe 100.

[0162] Step 820, controlling the ultrasonic probe through the front-end transceiver circuit so that the ultrasonic array element groups at different distribution positions on the ultrasonic probe respectively transmit unfocused ultrasonic waves to the target area in different preset transmission directions.

[0163] In this step, after the positions of the ultrasound array element groups with different transmission directions on the ultrasound probe 100 are determined through the above step 810, the processor 105 controls the transmitting circuit 101 to drive these different ultrasound array element groups to transmit unfocused ultrasound waves to the ROI area in turn in different transmission directions. For details on how different ultrasound array element groups transmit unfocused ultrasound waves in different transmission directions, please refer to the description of the above step 410 and related embodiments, which will not be repeated here.

[0164] In one embodiment, see Fig.10 As shown, the above step 412 specifically includes the following steps 1010 to 1020

[0165] Step 1010: determine the target emission direction of each ultrasound array element group in the ultrasound probe according to the boundary of the region of interest and the positions of array elements of at least two ultrasound array element groups distributed on the ultrasound probe.

[0166] In this step, the processor 105 obtains the ROI area set by the user according to the above-mentioned step 411 and its related embodiments, and determines the boundary of the ROI area according to the relevant parameters of the ROI area (such as the center position, the shape or size of the boundary, etc.), and then determines the target emission direction of the ultrasonic waves emitted by different ultrasonic array element groups according to the boundary of the ROI area and the positions of different ultrasonic array element groups on the ultrasonic probe (that is, the distribution positions of the array elements of each ultrasonic array element group on the ultrasonic probe).

[0167] In one embodiment, the processor 105 obtains the position of the ultrasonic array element group on the ultrasonic probe 100 that needs to be determined currently, that is, the position of the array elements of the ultrasonic array element group on the ultrasonic probe 100. Then, the target emission direction of the ultrasonic array element group to emit the ultrasonic wave is determined according to the boundary of the ROI area. In one embodiment, the boundary position of the array elements of the ultrasonic array element group on the ultrasonic probe can be determined first, that is, the position (or number) of the first array element of the ultrasonic array element group and the position (or number) of the last array element, and then, according to the boundary position of the ultrasonic array element group, the boundary line located on at least one side of the region of interest is determined, wherein the boundary line has one and only one intersection with the region of interest, for example, according to a point on the boundary between the first array element of the ultrasonic array element group and the ROI region, a boundary line that does not intersect with the ROI region except for the point is determined, and the direction of the boundary line relative to the plane of the ultrasonic probe 100 is the target emission direction. Among them, if the unfocused ultrasonic wave emitted by the ultrasonic array element group is a plane wave, the target emission direction of the current ultrasonic array element group can be determined after determining a boundary line. For the case where the unfocused ultrasonic wave is a divergent wave, the target emission direction of the current ultrasonic array element group can be determined according to the boundary lines on both sides of the ROI area.

[0168] In one embodiment, it is necessary to determine whether the target emission direction determined according to the boundary line is applicable, for example, the angle of the determined target emission direction does not meet the preset angle range, for example, the angle between the target emission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is greater than 45 degrees. For another example, the emission direction corresponding to the first boundary line determined by the first array element position of the ultrasound array element group and the first point of the ROI area boundary can only ensure that the ultrasound wave emitted by the first array element according to the emission direction can cover one side of the ROI area. For the last array element of the ultrasound array element group, the ultrasound wave emitted according to the emission normal may still intersect with the ROI area. Therefore, it is necessary to confirm whether the ultrasound wave emitted by the last array element in the ultrasound array element group according to the emission direction can cover the ROI area. If not, it is necessary to redetermine another target emission direction, for example, using the last array element of the ultrasound array element group and the second point of the ROI area boundary to redefine the boundary line, and then redetermine the target emission direction according to the new boundary line and verify its coverage range. If all boundary lines determined by the current ultrasound array element group and the ROI area boundary are not applicable, the user is prompted to reselect the ROI area or change the position of the current ultrasound array element group on the ultrasound probe 100.

[0169] The boundary of the ROI region may be in different shapes, such as a polygon, a circle, or an ellipse, wherein the polygon may also be a quadrilateral, a rectangle, a trapezoid, or the like.

[0170] In one embodiment, taking the ROI region as a polygon as an example, a position having only one intersection with the ROI region is a vertex of the polygon. Therefore, the boundary line located on at least one side of the ROI region can be determined according to the vertex of the ROI region and the position of the current ultrasound array element group, such as the position of the first array element or the last array element, and then the target emission direction can be determined.

[0171] In another embodiment, taking the ROI area as a circle as an example, at least one tangent line to the circle can be determined based on the first array element or the last array element of the ultrasound array element group, and the target emission direction can be determined based on the tangent line as a boundary line.

[0172] In one embodiment, the ROI region is a quadrilateral, and therefore, the position with only one intersection with the ROI region is the diagonal of the quadrilateral, so the boundary line can be determined according to the diagonal of the ROI region and the position of the current ultrasonic array element group, and then the target emission direction can be determined. That is, according to the diagonal of the ROI region and the positions of the array elements of at least two groups of ultrasonic array elements distributed on the ultrasonic probe, the target emission direction corresponding to each ultrasonic array element group in the ultrasonic probe is determined.

[0173] For example, see Figure 9aAs shown, the boundary of the ROI region 910 is a quadrilateral. For the array elements of the first ultrasonic array element group 501, the array elements are respectively from the array element numbered 51 to the array element numbered 210 of the ultrasonic probe 100. Then, the array element numbered 51 is connected to the vertex at the upper left corner of the ROI region 910 to obtain a first boundary line 920. The direction indicated by the arrow ① of the first boundary line 920 is the target emission direction corresponding to the first ultrasonic array element group 501. Similarly, for the second ultrasonic array element group 502, the distribution range of its array elements on the ultrasonic probe 100 is from the array elements numbered 65 to the array elements numbered 256. According to the first array element (array element numbered 65) in the second ultrasonic array element group 502 and the vertex at the upper left corner of the ROI region 910, a third boundary line 940 is obtained. The direction indicated by the arrow ② of the third boundary line 940 is the target emission direction corresponding to the second ultrasonic array element group 502. Of course, the vertex at the lower right corner of the ROI area 910 can also be used to connect the lines, for example, the array element numbered 210 is connected to the vertex at the lower right corner of the ROI area 910 to obtain a second boundary line 930, and the direction indicated by the arrow ① of the second boundary line 930 is the target emission direction corresponding to the first ultrasonic array element group 501.

[0174] Figure 9a In another embodiment, different ultrasonic array element groups may use the same diagonal angle to determine the boundary line, and then determine the target emission direction of the ultrasonic array element group. In another embodiment, different ultrasonic array element groups may use different diagonal angles to determine the target emission direction of the ultrasonic array element group. For example, see Figure 9b As shown, the first ultrasound array element group 501 uses the lower left corner or the upper right corner of the ROI area 910 to determine the boundary line, and the second ultrasound array element group 502 uses the upper left corner or the lower right corner of the ROI area 910 to determine the boundary line.

[0175] In one embodiment, in order to avoid the loss of measurement data at the border position of the ROI area 910, in some embodiments, a certain margin distance can be reserved to cover the transmission range of the ultrasonic wave of the appropriate ultrasonic array element group, for example, see Fig.9e As shown, taking the first ultrasonic array element group 501 as an example, a first boundary line 920 is determined according to the array element numbered 51 in the first ultrasonic array element group 501 and the upper left corner of the ROI area 910. Fig.9eIn the embodiment, the direction of the first boundary line 920 is not directly used as the target emission direction, but the direction of the first boundary line 920 is offset upward by a certain angle (i.e., the angle with the normal direction of the plane where the array element of the ultrasonic probe is located is increased) so that a certain margin distance is reserved between the ultrasonic emission boundary indicated by arrow ① and the ROI area 910. Of course, in addition to increasing the angle with the normal direction of the plane where the array element of the ultrasonic probe is located, the ROI area 910 can also be expanded when determining the diagonal of the ROI area 910, that is, after increasing the area of ​​the ROI area 910, the first boundary line 920 is determined according to the diagonal of the ROI area 910 after the area is increased, so that a certain distance can be reserved between the coverage range of the ultrasonic wave emitted by the ultrasonic array element group finally determined and the boundary of the ROI area 910.

[0176] Step 1020: Control at least two groups of ultrasound array elements through the front-end transceiver circuit to transmit unfocused ultrasound to the target area in different target transmission directions.

[0177] In this step, after the target emission directions of different ultrasound array element groups are determined through the above step 1010, the processor 105 controls the transmitting circuit 101 to drive these different ultrasound array element groups to sequentially emit unfocused ultrasound waves to the ROI area in different target emission directions. For details on how different ultrasound array element groups emit unfocused ultrasound waves in different emission directions, please refer to the description of the above step 410 and related embodiments, which will not be repeated here.

[0178] In one embodiment, the process of executing the above steps 420 to 430 specifically includes the following steps:

[0179] Perform beam synthesis at least twice with different beam synthesis directions on at least one group of non-focused ultrasonic echo signals to obtain at least two groups of received signals with different beam synthesis directions corresponding to one emission direction, and obtain at least two blood flow velocity components corresponding to one emission direction based on the at least two groups of received signals, wherein each group of received signals includes non-focused ultrasonic waves emitted at least twice in one emission direction.

[0180] In one embodiment of this step, the ultrasound probe 100 receives an echo of an ultrasound wave in a transmission direction. If the echo of the ultrasound wave in the transmission direction is directly beamformed, a receiving signal (echo signal) corresponding to this direction can be obtained, and the beamformed direction of the beamformed signal is the transmission direction of the ultrasound wave of the ultrasound array element group. For example, the ultrasound wave emitted by the first ultrasound array element group 501 is beamformed in a first beamformed direction, and the first beamformed direction is the same as the first transmission direction. The synthesized first receiving signal corresponds to the first transmission direction, and the operation of the above step 430 is performed on the first receiving signal to obtain the blood flow velocity component in the first transmission direction.

[0181] In addition, if the ultrasound waves emitted by the same first ultrasound array element group 501 are beamsynthesized in other beamsynthesis directions, for example, the ultrasound waves emitted by the first ultrasound array element group 501 are beamsynthesized in the second beamsynthesis direction, and the second beamsynthesis direction is different from the first emission direction, then the synthesized second receiving signal, that is, the signal corresponding to the first emission direction (because it is obtained based on the echo of the ultrasound waves in the first emission direction), also corresponds to the second beamsynthesis direction, and the second receiving signal is operated as in the above step 430, so that the blood flow velocity component in the second beamsynthesis direction can be obtained. Through the above steps, blood flow velocity components at multiple angles can be obtained, which is helpful to improve the velocity measurement accuracy of blood flow velocity vector imaging.

[0182] By controlling the apodization parameters of the beam synthesis of the beam synthesis circuit 104, it is possible to adjust the position of the ultrasound array element group receiving the ultrasound echo and / or the beam synthesis direction. For example, at least one group of unfocused ultrasound echo signals is subjected to at least two beam synthesiss with different beam synthesis directions and / or array elements used for beam synthesis, to obtain at least two receiving signals corresponding to one transmission direction in different beam synthesis directions, and to obtain at least two blood flow velocity components corresponding to one transmission direction according to the at least two receiving signals.

[0183] See also Fig.11a As shown, taking the first ultrasonic array element group 501 as an example, arrow ① indicates the first transmission direction of the first ultrasonic array element group 501. By applying the apodization function 1110 to the beamforming circuit 104, the coverage range of the apodization function 1110 is the position range of the ultrasonic array element group receiving ultrasonic waves on the ultrasonic probe 100. The curve of the apodization function 1110 indicates the reception delay control of each array element within the position range. The principle is the same as that of adjusting the transmission direction in the above text. By changing the reception time of each array element, the reception angle of the ultrasonic wave can be changed, that is, the above-mentioned beamforming direction is adjusted. For example Fig.11a The direction indicated by the straight line ④ is the beam synthesis direction adjusted by the apodization function 1110. Figure 1The apodization function 1110 in the embodiment controls the position of the ultrasonic array element group receiving the ultrasonic echo and controls the beam synthesis direction.

[0184] In one embodiment, the array elements of the ultrasound array element group for transmitting non-focused ultrasound and the ultrasound array element group for receiving echoes of non-focused ultrasound corresponding to the same transmission direction are distributed at the same position on the ultrasound probe, that is, the same ultrasound array element group is used for transmitting ultrasound and receiving ultrasound.

[0185] In another embodiment, the array elements of the ultrasound array element group for receiving the echo of the non-focused ultrasound wave corresponding to the same transmission direction are distributed on the ultrasound probe within the range of the ultrasound array element group for transmitting the non-focused ultrasound wave. That is, the ultrasound array element group for receiving the ultrasound wave is a subset of the ultrasound array element group for transmitting the ultrasound wave. For example Fig.11a As shown, the ultrasound array element group 1120 receiving the ultrasound wave is still within the range of the first ultrasound array element group 501 .

[0186] In another embodiment, the ultrasonic array element group for transmitting non-focused ultrasonic waves and the ultrasonic array element group for receiving echoes of non-focused ultrasonic waves corresponding to the same transmission direction have multiple array elements at the same position distributed on the ultrasonic probe and at least one array element at a different position. That is, the ultrasonic array element group for transmitting ultrasonic waves and the ultrasonic array element group for receiving ultrasonic waves partially overlap on the ultrasonic probe 100. For example Fig.11b As shown, the ultrasonic array element group for receiving ultrasonic echoes corresponding to the first ultrasonic array element group 501 (i.e., the array elements covered by the apodization function 1110) partially overlaps with the first ultrasonic array element group 501, and the ultrasonic array element group for receiving ultrasonic echoes corresponding to the second ultrasonic array element group 502 (i.e., the array elements covered by the apodization function 1120) partially overlaps with the second ultrasonic array element group 502.

[0187] In another embodiment, the array elements of the ultrasonic array element group for transmitting non-focused ultrasonic waves and the ultrasonic array element group for receiving echoes of non-focused ultrasonic waves corresponding to the same transmission direction are distributed at completely different positions on the ultrasonic probe. That is, the ultrasonic array element group for transmitting ultrasonic waves and the ultrasonic array element group for receiving ultrasonic waves are distributed completely on the ultrasonic probe 100 (that is, the two ultrasonic array element groups do not overlap at all).

[0188] When the ultrasonic array element groups for transmitting and receiving ultrasonic waves are completely different or partially overlap, there may be potential problems. Since it takes a certain amount of time to start an element, for example, there is a target element for receiving ultrasonic waves that is not in the ultrasonic array element group for transmitting ultrasonic waves. Then, after the ultrasonic array element group transmits ultrasonic waves, it takes a certain amount of time to start the target element so that the target element can receive the ultrasonic wave echo. Assuming that the time for starting the target element is T1, and the time from transmitting the ultrasonic wave to receiving the ultrasonic wave is T2, when T2 is greater than T1, the target element receives the ultrasonic wave echo only after it is started, so the ultrasonic wave echo can be received normally. When T2 is less than T1, the target element has not yet been started, and the ultrasonic wave echo has reached the ultrasonic probe 100, which will cause part of the ultrasonic wave echo signal to be lost.

[0189] Therefore, in one embodiment, when the ultrasonic array element group for transmitting non-focused ultrasonic waves and the ultrasonic array element group for receiving echoes of non-focused ultrasonic waves corresponding to the same transmission direction have multiple array elements at the same position and at least one array element at different positions distributed on the ultrasonic probe, the distance between the region of interest and the ultrasonic probe is greater than or equal to the first threshold. By controlling the distance between the region of interest and the ultrasonic probe 100, the above-mentioned echo time T2 can be adjusted so that T2 is greater than T1, so that the echo signal of the ultrasonic wave can be received normally.

[0190] Similarly, in another embodiment, when the array elements of the ultrasonic array element group for transmitting unfocused ultrasonic waves and the ultrasonic array element group for receiving echoes of unfocused ultrasonic waves corresponding to the same transmission direction are distributed at completely different positions on the ultrasonic probe, the distance between the region of interest and the ultrasonic probe is greater than or equal to the first threshold. In the above embodiment, the available range of the ROI area set by the user can be limited according to different control modes of the ultrasonic imaging device 10. For example, when the ultrasonic array element groups for transmitting and receiving ultrasonic waves are the same or mutually inclusive, the setting range of the ROI area is not limited. In addition, the available range of the ROI area set by the user is controlled so that the distance between the ROI area and the ultrasonic probe is greater than or equal to the first threshold.

[0191] See also Fig.12 As shown, an ultrasonic imaging method provided by an embodiment of the present application may include but is not limited to the following steps 1210 to 1240:

[0192] Step 1210: Control at least two groups of ultrasound array elements on the ultrasound probe through the front-end transceiver circuit to transmit unfocused ultrasound waves to the target area in different transmission directions.

[0193] Among them, the angle between the above-mentioned transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein each group of ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that are less than or equal to the number of all transceiver channels and each group of ultrasonic array element groups has a plurality of array elements at the same position distributed on the ultrasonic probe and at least one array element at a different position.

[0194] In another embodiment, the positions of the array elements included in at least two groups of ultrasound array elements on the ultrasound probe are completely different, that is, the positions of the ultrasound array elements of at least two groups on the ultrasound probe 100 have no overlapping parts.

[0195] In this step, how different ultrasonic array element groups transmit unfocused ultrasonic waves in different transmission directions is specifically described in the above step 410 and related embodiments, and will not be repeated here.

[0196] Step 1220, controlling the ultrasonic probe to receive the echo of the unfocused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the unfocused ultrasonic wave corresponding to different transmission directions.

[0197] In this step, a group of unfocused ultrasonic echo signals includes unfocused ultrasonic waves emitted at least twice in a corresponding emission direction. How to receive the unfocused ultrasonic echoes through the ultrasonic probe is described in the above step 420 and related embodiments, which will not be repeated here.

[0198] Step 1230: Compound the at least two groups of unfocused ultrasonic echo signals to obtain a compounded echo signal.

[0199] In this step, the processor 105 performs composite processing on the echo signals of each group of non-focused ultrasound waves in different emission directions obtained by the receiving circuit 103 to obtain composite echo signals. In one embodiment, a beamforming algorithm can be used to perform composite processing on the echo signals of ultrasound waves in different emission directions, wherein different beamforming parameters can be set to realize the processing of blood flow velocity component data in different emission directions during the beamforming process. For example, by setting matrix parameters, the reconstruction of blood flow velocity components in different emission directions can be completed during the signal composite process, so that the obtained echo signal can reflect the blood flow velocity vector information of the target area. In another embodiment, the echo signals of non-focused ultrasound waves in different emission directions can also be input into a pre-trained machine learning model for composite processing to obtain composite echo signals.

[0200] Step 1240: Obtain an ultrasonic image or blood flow velocity according to the composite echo signal.

[0201] In this step, the processor 105 processes the composite echo signal to obtain an ultrasonic image or blood flow velocity, which may be a superimposed display of a B image and a blood flow image, or display of blood flow velocity parameters.

[0202] In one embodiment, the blood flow velocity vector image includes blood flow velocity vector markers for each target position in the target area, that is, the blood flow velocity vector is represented by a dynamic or static marker on the ultrasound image, wherein the direction of the marker represents the velocity direction of the blood flow velocity vector, and the size or transparency of the marker represents the velocity magnitude of the blood flow velocity vector. The blood flow velocity vector is represented by a dynamic marker on the ultrasound image, including: the position of the marker on two adjacent frames of ultrasound images is dynamically updated to form a flow-like effect that changes with time, wherein the position of the marker represents the corresponding position of the blood flow in the vascular tissue.

[0203] In one embodiment, it should be noted that the dynamic display of the blood flow velocity vector image can be presented by displaying dynamic markers on the ultrasound image. The specific implementation can refer to the following description: First, the size and direction of the blood flow velocity vector of the current frame blood flow is obtained, and then some markers are randomly displayed in the ultrasound image of the vascular tissue. Among them, these markers can be symbols such as arrows, triangles, circles, etc. According to the size and direction of the blood flow velocity vector corresponding to the position of each marker in the current frame, combined with the time interval between two adjacent frames, the position of the marker in the next frame is calculated, and then the marker is displayed. Similarly, when several frames of images are displayed together, the flow effect of blood flow can be visually presented.

[0204] An ultrasonic imaging device provided in one embodiment of the present application includes:

[0205] Ultrasound probe;

[0206] a transmitting / receiving circuit, used to control the ultrasonic probe to transmit ultrasonic waves to the blood vessel area of ​​the target object and receive echoes of the ultrasonic waves;

[0207] A processor, used for processing ultrasonic echoes to obtain a tissue image and / or a blood flow velocity vector image of a blood vessel region;

[0208] A display, used for displaying the tissue image and / or the blood flow velocity vector image;

[0209] The processor is also used to execute the blood flow velocity vector imaging method provided by any one of the above embodiments, or to execute the ultrasound imaging method provided by any one of the above embodiments.

[0210] An embodiment of the present application provides an electronic device, including a memory and a processor, wherein the memory stores a computer program, and when the processor executes the computer program, it implements a blood flow velocity vector imaging method as provided in any one of the above embodiments, or executes an ultrasound imaging method as provided in any one of the above embodiments.

[0211] An embodiment of the present application provides a computer storage medium on which a computer program is stored, which is applied to an ultrasonic imaging device. When the computer program is executed by a processor, a blood flow velocity vector imaging method as provided in any one of the above embodiments is implemented, or an ultrasonic imaging method provided in any one of the above embodiments is executed.

[0212] The embodiment of the present application provides a computer program product or a computer program, which includes a computer instruction stored in a computer-readable storage medium. The processor of the computer device reads the computer instruction from the computer-readable storage medium, and the processor executes the computer instruction, so that the computer device executes the blood flow velocity vector imaging method provided by any of the above embodiments, or executes the ultrasound imaging method provided by any of the above embodiments.

[0213] In the several embodiments provided in the present application, it should be understood that the disclosed systems, devices and methods can be implemented in other ways. For example, the device embodiments described above are only schematic. For example, the division of units is only a logical function division. There may be other division methods in actual implementation, such as multiple units or components can be combined or integrated into another system, or some features can be ignored or not executed. Another point is that the mutual coupling or direct coupling or communication connection shown or discussed can be an indirect coupling or communication connection through some interfaces, devices or units, which can be electrical, mechanical or other forms.

[0214] The units described as separate components may or may not be physically separated, and the components shown as units may or may not be physical units, that is, they may be located in one place or distributed on multiple network units. Some or all of the units may be selected according to actual needs to achieve the purpose of the solution of this embodiment.

[0215] In addition, each functional unit in each embodiment of the present application may be integrated into one processing unit, or each unit may exist physically separately, or two or more units may be integrated into one unit. The above-mentioned integrated unit may be implemented in the form of hardware or in the form of software functional units.

[0216] If the integrated unit is implemented in the form of a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the present application is essentially or the part that contributes to the prior art or all or part of the technical solution can be embodied in the form of a software product, and the computer software product is stored in a storage medium, including a number of instructions to enable a computer device (which can be a personal computer, a server, or a network device, etc.) to perform all or part of the steps of the various embodiments of the present application. The aforementioned storage medium includes: U disk, mobile hard disk, read-only memory (Read-Only Memory, referred to as ROM), random access memory (Random Access Memory, referred to as RAM), disk or optical disk and other media that can store program codes.

[0217] It should also be understood that the various implementations provided in the embodiments of the present application can be combined arbitrarily to achieve different technical effects.

[0218] The above is a specific description of the preferred implementation of the present application, but the present application is not limited to the above implementation mode. Technical personnel familiar with the field can also make various equivalent modifications or substitutions under the shared conditions without violating the spirit of the present application. These equivalent modifications or substitutions are all included in the scope defined by the claims of the present application.

Claims

1. A blood flow velocity vector imaging method, characterized in that: The method comprises: Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe by a front-end transceiver circuit to transmit non-focused ultrasonic waves to the target area in different transmission directions, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein one group of the ultrasonic array element groups corresponds to one transmission direction, each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and each group of the ultrasonic array element groups includes a plurality of array elements at the same position and at least one array element at a different position distributed on the ultrasonic probe; Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction; According to at least two groups of echo signals of the non-focused ultrasound, at least two blood flow velocity components corresponding to different emission directions are obtained, wherein one of the emission directions corresponds to one of the blood flow velocity components; Reconstructing the velocity of the at least two blood flow velocity components in different emission directions to obtain blood flow velocity vector data of the target area; obtaining a blood flow velocity vector image of the target area based on the blood flow velocity vector data of the target area; The blood flow velocity vector image is displayed.

2. The blood flow velocity vector imaging method according to claim 1, characterized in that: The method of controlling at least two groups of ultrasound array elements on the ultrasound probe to transmit non-focused ultrasound waves to the target area in different transmission directions respectively by the front-end transceiver circuit includes: Acquire a region of interest in the target area; According to the region of interest, at least two groups of ultrasound array elements on the ultrasound probe are controlled by the front-end transceiver circuit to transmit unfocused ultrasound waves to the target area in different transmission directions, wherein the unfocused ultrasound waves emitted by different ultrasound array element groups all cover the region of interest.

3. The blood flow velocity vector imaging method according to claim 2, characterized in that: The region of interest is obtained by following the steps below: Controlling the ultrasonic probe to send a first ultrasonic wave to the target area, receiving an echo of the first ultrasonic wave returned by the target area, and obtaining an echo signal of the first ultrasonic wave; Obtaining a tissue image of the target area according to the echo signal of the first ultrasonic wave; The tissue image is displayed and the region of interest set in the tissue image is acquired.

4. The blood flow velocity vector imaging method according to claim 2 is characterized in that , the controlling of at least two groups of ultrasound array elements on the ultrasound probe by the front-end transceiver circuit according to the region of interest to transmit non-focused ultrasound to the target region in different transmission directions respectively, comprises: Determining distribution positions of array elements of each of the ultrasound array element groups in the ultrasound probe on the ultrasound probe according to the boundary of the region of interest and different preset transmission directions of at least two groups of ultrasound array element groups; The ultrasonic probe is controlled by the front-end transceiver circuit so that the ultrasonic array element groups at different distribution positions on the ultrasonic probe respectively transmit the unfocused ultrasonic waves to the target area in different preset transmission directions.

5. The blood flow velocity vector imaging method according to claim 4, characterized in that: In at least two groups of the ultrasound array element groups, the positions of the array elements of each group of the ultrasound array element groups distributed on the ultrasound probe are obtained by the following steps: Determine two boundary lines on both sides of the boundary of the region of interest according to the preset transmission direction corresponding to the ultrasound array element group, wherein the boundary line has one and only one intersection point with the region of interest; The positions of the array elements in the ultrasound array element group distributed on the ultrasound probe are determined according to the two boundary lines.

6. The blood flow velocity vector imaging method according to claim 4, characterized in that: The step of determining the positions of array elements of each of the ultrasound array element groups in the ultrasound probe distributed on the ultrasound probe according to the boundary of the region of interest and different preset transmission directions of at least two groups of ultrasound array element groups includes at least one of the following: Determine the positions of array elements of each of the ultrasound array element groups in the ultrasound probe distributed on the ultrasound probe according to the vertices of the region of interest and different preset transmission directions of at least two groups of ultrasound array element groups, wherein the region of interest is a polygon; Alternatively, the positions of array elements of each of the ultrasound array element groups in the ultrasound probe on the ultrasound probe are determined according to the diagonal angle of the region of interest and different preset transmission directions of at least two groups of the ultrasound array element groups, wherein the region of interest is a quadrilateral, and the diagonals corresponding to different ultrasound array element groups are the same or different; Alternatively, the positions of the array elements on the ultrasound probe are determined based on the projection of the region of interest on the plane where the array elements of the ultrasound probe are located, wherein the ultrasound array element group includes the array elements covered by the projection of the region of interest on the plane where the array elements of the ultrasound probe are located.

7. The blood flow velocity vector imaging method according to claim 2 is characterized in that , the controlling of at least two groups of ultrasound array elements on the ultrasound probe by the front-end transceiver circuit according to the region of interest to transmit non-focused ultrasound to the target region in different transmission directions respectively, comprises: Determining a target emission direction of each of the ultrasound array element groups in the ultrasound probe according to a boundary of the region of interest and positions of the array elements of at least two groups of the ultrasound array element groups distributed on the ultrasound probe; At least two groups of the ultrasound array elements are controlled by the front-end transceiver circuit to transmit the unfocused ultrasound to the target area in different target transmission directions.

8. The blood flow velocity vector imaging method according to claim 7, characterized in that: In at least two groups of the ultrasound array element groups, the target emission direction of the non-focused ultrasound waves emitted by each group of the ultrasound array element groups is obtained by the following steps: Determining boundary positions of the array elements of the ultrasound array element group distributed on the ultrasound probe; Determining a boundary line located on at least one side of the region of interest according to the boundary position of the ultrasound array element group, wherein the boundary line has one and only one intersection point with the region of interest; The target emission direction is determined according to at least one of the boundary lines.

9. The blood flow velocity vector imaging method according to claim 7, characterized in that: Determining the target emission direction of each of the ultrasound array element groups in the ultrasound probe according to the boundary of the region of interest and the positions of the array elements of at least two groups of the ultrasound array element groups distributed on the ultrasound probe comprises at least one of the following: Determine the target emission direction corresponding to each of the ultrasound array element groups in the ultrasound probe according to the vertices of the region of interest and the positions of the array elements of at least two groups of the ultrasound array element groups distributed on the ultrasound probe, wherein the region of interest is a polygon; Alternatively, the target emission direction corresponding to each of the ultrasonic array element groups in the ultrasonic probe is determined based on the diagonal of the region of interest and the positions of the array elements of at least two groups of the ultrasonic array element groups distributed on the ultrasonic probe, wherein the region of interest is a quadrilateral and the diagonals corresponding to different ultrasonic array element groups are the same or different.

10. The blood flow velocity vector imaging method according to any one of claims 1 to 2, 8 to 9, characterized in that: The number of array elements in different ultrasound array element groups is the same.

11. The blood flow velocity vector imaging method according to claim 1, characterized in that: It comprises three groups of ultrasonic array element groups, wherein the emission directions of the unfocused ultrasonic waves emitted by the three groups of ultrasonic array element groups are respectively a first emission direction, a second emission direction and a third emission direction, wherein the third emission direction is perpendicular to the plane where the ultrasonic probe is located, and the angles between the first emission direction and the second emission direction and the third emission direction are greater than 0 degree and less than or equal to 45 degrees, and the first emission direction and the second emission direction deviate from the left and right sides of the third emission direction respectively.

12. The blood flow velocity vector imaging method according to claim 1, characterized in that: The number of array elements on the ultrasonic probe is 256, and the number of all transceiver channels of the front-end transceiver circuit is greater than or equal to 96 and less than or equal to 192.

13. The blood flow velocity vector imaging method according to claim 2, characterized in that: Also includes at least one of the following: When the ultrasound array element group for transmitting the unfocused ultrasound wave and the ultrasound array element group for receiving the echo of the unfocused ultrasound wave corresponding to the same transmission direction have a plurality of array elements at the same position and at least one array element at a different position distributed on the ultrasound probe, the distance between the region of interest and the ultrasound probe is greater than or equal to a first threshold; Alternatively, when the array elements of the ultrasound array element group for transmitting the unfocused ultrasound and the ultrasound array element group for receiving the echo of the unfocused ultrasound corresponding to the same transmission direction are distributed at completely different positions on the ultrasound probe, the distance between the region of interest and the ultrasound probe is greater than or equal to a first threshold.

14. A blood flow velocity vector imaging method, characterized in that: The method comprises: Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe to transmit non-focused ultrasonic waves to the target area in different transmission directions respectively through the front-end transceiver circuit, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and the positions of the plurality of array elements included in at least two groups of the ultrasonic array element groups on the ultrasonic probe are completely different; Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction; According to at least two groups of echo signals of the non-focused ultrasound, at least two blood flow velocity components corresponding to different emission directions are obtained, wherein one of the emission directions corresponds to one of the blood flow velocity components; Reconstructing the velocity of the at least two blood flow velocity components in different emission directions to obtain blood flow velocity vector data of the target area; obtaining a blood flow velocity vector image of the target area based on the blood flow velocity vector data of the target area; The blood flow velocity vector image is displayed.

15. The blood flow velocity vector imaging method according to claim 14, characterized in that: The method of controlling at least two groups of ultrasound array elements on the ultrasound probe to transmit non-focused ultrasound waves to the target area in different transmission directions respectively by the front-end transceiver circuit includes: Acquire a region of interest in the target area; According to the region of interest, at least two groups of ultrasound array elements on the ultrasound probe are controlled by the front-end transceiver circuit to transmit unfocused ultrasound waves to the target area in different transmission directions, wherein the unfocused ultrasound waves emitted by different ultrasound array element groups all cover the region of interest.

16. The blood flow velocity vector imaging method according to claim 15, characterized in that: The region of interest is obtained by following the steps below: Controlling the ultrasonic probe to send a first ultrasonic wave to the target area, receiving an echo of the first ultrasonic wave returned by the target area, and obtaining an echo signal of the first ultrasonic wave; Obtaining a tissue image of the target area according to the echo signal of the first ultrasonic wave; The tissue image is displayed and the region of interest set in the tissue image is acquired.

17. The blood flow velocity vector imaging method according to claim 15, characterized in that: The controlling at least two groups of ultrasound array elements on the ultrasound probe to transmit non-focused ultrasound to the target area in different transmission directions respectively through the front-end transceiver circuit according to the region of interest comprises: Determining distribution positions of array elements of each of the ultrasound array element groups in the ultrasound probe on the ultrasound probe according to the boundary of the region of interest and different preset transmission directions of at least two groups of ultrasound array element groups; The ultrasonic probe is controlled by the front-end transceiver circuit so that the ultrasonic array element groups at different distribution positions on the ultrasonic probe respectively transmit the unfocused ultrasonic waves to the target area in different preset transmission directions.

18. The blood flow velocity vector imaging method according to claim 14, characterized in that: The controlling at least two groups of ultrasound array elements on the ultrasound probe to transmit non-focused ultrasound to the target area in different transmission directions respectively through the front-end transceiver circuit according to the region of interest comprises: Determining a target emission direction of each of the ultrasound array element groups in the ultrasound probe according to a boundary of the region of interest and positions of the array elements of at least two groups of the ultrasound array element groups distributed on the ultrasound probe; At least two groups of the ultrasound array elements are controlled by the front-end transceiver circuit to transmit the unfocused ultrasound to the target area in different target transmission directions.

19. The blood flow velocity vector imaging method according to claim 4, characterized in that: Also includes at least one of the following: When the ultrasound array element group for transmitting the unfocused ultrasound wave and the ultrasound array element group for receiving the echo of the unfocused ultrasound wave corresponding to the same transmission direction have a plurality of array elements at the same position and at least one array element at a different position distributed on the ultrasound probe, the distance between the region of interest and the ultrasound probe is greater than or equal to a first threshold; Alternatively, when the array elements of the ultrasound array element group for transmitting the unfocused ultrasound and the ultrasound array element group for receiving the echo of the unfocused ultrasound corresponding to the same transmission direction are distributed at completely different positions on the ultrasound probe, the distance between the region of interest and the ultrasound probe is greater than or equal to a first threshold.

20. An ultrasonic imaging method, characterized in that: The method comprises: Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe by a front-end transceiver circuit to transmit non-focused ultrasonic waves to the target area in different transmission directions, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and each group of the ultrasonic array element groups includes a plurality of array elements at the same position distributed on the ultrasonic probe and at least one array element at a different position; Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction; Compounding at least two groups of non-focused ultrasonic echo signals to obtain a compounded echo signal; An ultrasonic image or blood flow velocity is obtained according to the composite echo signal.

21. An ultrasonic imaging method, characterized in that: The method comprises: Controlling at least two groups of ultrasonic array element groups on the ultrasonic probe to transmit non-focused ultrasonic waves to the target area in different transmission directions respectively through the front-end transceiver circuit, wherein the angle between the transmission direction and the normal direction of the plane where the array element of the ultrasonic probe is located is less than or equal to 45 degrees and the number of all transceiver channels of the front-end transceiver circuit is less than the number of all array elements distributed on the ultrasonic probe; wherein each group of the ultrasonic array element groups includes a plurality of array elements distributed on the ultrasonic probe that is less than or equal to the number of all transceiver channels and the positions of the plurality of array elements included in at least two groups of the ultrasonic array element groups on the ultrasonic probe are completely different; Controlling the ultrasonic probe to receive the echo of the non-focused ultrasonic wave returned from the target area through the front-end transceiver circuit, and obtaining at least two groups of echo signals of the non-focused ultrasonic wave corresponding to different emission directions, wherein one group of echo signals of the non-focused ultrasonic wave includes the non-focused ultrasonic wave emitted at least twice in one emission direction; Compounding at least two groups of non-focused ultrasonic echo signals to obtain a compounded echo signal; An ultrasonic image or blood flow velocity is obtained according to the composite echo signal.

22. An ultrasonic imaging device, characterized in that: include: Ultrasound probe; a transmitting / receiving circuit, the transmitting / receiving circuit being used to control the ultrasonic probe to transmit ultrasonic waves to the blood vessel region of the target object and to receive echoes of the ultrasonic waves; A processor, the processor being used to process the ultrasonic echo to obtain a tissue image and / or a blood flow velocity vector image of the blood vessel region; a display, the display being used to display the tissue image and / or the blood flow velocity vector image; The processor is also used to execute the blood flow velocity vector imaging method described in any one of claims 1 to 19, or to execute the ultrasound imaging method described in any one of claims 20 to 21.

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