An ultrasonic diagnostic instrument, ultrasonic imaging method, apparatus, and media

Abstract

The application relates to the technical field of ultrasonic imaging, in particular to an ultrasonic diagnostic instrument, an ultrasonic imaging method, an ultrasonic imaging device and a medium, which are used for rearranging the collection sequences of focused beams and plane beams, so that the foreground imaging frame frequency is not limited by the frame packet length. The method comprises the following steps: in response to an ultrasonic image generation instruction, alternately emitting a first beam set and a second beam set; based on the collection data of N focused beams corresponding to the nth+1 frame, generating a background image corresponding to the nth+1 frame; and based on the collection data of Et plane beams corresponding to the nth+1 frame, generating a foreground image corresponding to the nth+1 frame, the first Et-N plane beams in the Et plane beams corresponding to the nth+1 frame are the last Et-N plane beams in the Et plane beams corresponding to the nth frame; wherein n, Et and N are positive integers; based on the background image and the foreground image corresponding to each frame of ultrasonic image, the ultrasonic image of the corresponding frame is synthesized.

Description

Technical Field

[0001] This application relates to the field of ultrasound imaging technology, and in particular to an ultrasound diagnostic instrument, ultrasound imaging method, device and medium. Background Technology

[0002] Ultrasonic plane wave imaging is a novel imaging technique that works by simultaneously exciting all transducers on the emission aperture, causing the probe to emit sound waves with plane wave characteristics, covering the entire imaging area in a single emission. Therefore, compared to traditional focused beam imaging, plane wave imaging increases data acquisition efficiency by several to tens of times, significantly improving the speed sensitivity and spatial resolution of blood flow imaging.

[0003] However, because plane wave imaging lacks emission focusing capability, its performance in ultrasound grayscale images is inferior to that of traditional focused beam imaging. To ensure image quality, when performing blood flow imaging, the foreground blood flow image is acquired using a plane beam, while the background grayscale image is acquired using a focused beam.

[0004] However, the transmission modes of planar beams and focused beams are different. When designing the acquisition timing of planar beams, if the acquisition timing of focused beams is used, the acquisition time of focused beams will limit the acquisition time of planar beams, thereby limiting the ensemble length of blood flow imaging, and ultimately limiting the performance improvement of blood flow imaging. Summary of the Invention

[0005] The purpose of this application is to provide an ultrasound diagnostic instrument, ultrasound imaging method, device, and medium for rearranging the acquisition sequence of the focused beam and the planar beam so that the foreground imaging frame rate is not limited by the frame packet length.

[0006] In a first aspect, embodiments of this application provide an ultrasound imaging method, the method comprising:

[0007] In response to an instruction to generate an ultrasound image for a target region, a first beam set and a second beam set are alternately transmitted; the first beam set includes at least one focused beam, and the second beam set includes at least one planar beam.

[0008] For the (n+1)th frame of ultrasound image, a background image corresponding to the (n+1)th frame of ultrasound image is generated based on the acquisition data of N focused beams corresponding to the (n+1)th frame, where the N focused beams are adjacent focused beams; and a foreground image corresponding to the (n+1)th frame of ultrasound image is generated based on the acquisition data of Et planar beams corresponding to the (n+1)th frame, where the Et planar beams are adjacent planar beams, and the first Et-N planar beams in the Et planar beams corresponding to the (n+1)th frame are the last Et-N planar beams in the Et planar beams corresponding to the nth frame; where n, Et, and N are positive integers;

[0009] The ultrasound images of the corresponding frames are synthesized based on the background and foreground images corresponding to each frame of ultrasound image.

[0010] In some possible implementations, each N adjacent focused beams correspond to different scan line regions of the target area; each A adjacent planar beams correspond to different emission angles.

[0011] Where A is a positive integer, and Et and N are multiples of A.

[0012] In some possible implementations, if each first beam set includes a focused beam and each second beam set includes a planar beam, then:

[0013] The N focused beams corresponding to the above-mentioned (n+1)th frame are: the focused beams included in the N×n+1 to N×(n+1)th first beam sets;

[0014] The Et planar beams corresponding to the above-mentioned n+1 frame are the planar beams included in the N×n+1 to N×n+Et second beam sets.

[0015] In some possible implementations, if each first beam set includes a focused beam and each second beam set includes A planar beams, then:

[0016] The N focused beams corresponding to the above-mentioned (n+1)th frame are: the focused beams included in the N×n+1 to N×(n+1)th first beam sets;

[0017] The Et planar beam corresponding to the above-mentioned n+1 frame is the planar beam included in the second beam set from the N×n+1 to the N×n+Et / A.

[0018] In some possible implementations, if each first beam set includes k focused beams and each second beam set includes a planar beam, where k is a positive integer and N is a multiple of k, then:

[0019] The N focused beams corresponding to the above-mentioned (n+1)th frame are: the focused beams included in the first beam set from the N×n / k+1th to the N×(n+1) / kth frame;

[0020] The Et planar beams corresponding to the above-mentioned (n+1)th frame are the planar beams included in the second beam set from the N×n / k+1th to the N×n / k+Etth.

[0021] In some possible implementations, when alternately transmitting the first beam set and the second beam set, the method further includes:

[0022] After transmitting any of the aforementioned second beam sets, the first beam set is transmitted after a preset idle time corresponding to any of the aforementioned second beam sets.

[0023] In some possible implementations, the method further includes:

[0024] For the first frame of ultrasound image, a background image corresponding to the first frame of ultrasound image is generated based on the acquisition data of N focused beams corresponding to the first frame; and a foreground image corresponding to the first frame of ultrasound image is generated based on the acquisition data of Et planar beams corresponding to the first frame; and the first frame of ultrasound image is synthesized based on the background image and the foreground image corresponding to the first frame of ultrasound image.

[0025] Secondly, embodiments of this application also provide an ultrasound imaging device, the device comprising:

[0026] The transmitting module is configured to alternately transmit a first beam set and a second beam set in response to an ultrasound image generation command for a target area; the first beam set includes at least one focused beam, and the second beam set includes at least one planar beam.

[0027] The generation module is used to generate a background image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of N focused beams corresponding to the (n+1)th frame, wherein the N focused beams are adjacent focused beams; and to generate a foreground image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of Et planar beams corresponding to the (n+1)th frame, wherein the Et planar beams are adjacent planar beams, and the first Et-N planar beams of the Et planar beams corresponding to the (n+1)th frame are the last Et-N planar beams of the Et planar beams corresponding to the nth frame; wherein n, Et, and N are positive integers.

[0028] The synthesis module is used to synthesize ultrasound images of corresponding frames based on the background and foreground images corresponding to each frame of ultrasound image.

[0029] Thirdly, embodiments of this application also provide an ultrasound diagnostic instrument, including a probe and a processor;

[0030] A probe is placed in a target area of ​​the human body and, in response to an ultrasound image generation command for the target area, alternately emits a first beam set and a second beam set; the first beam set includes at least one focused beam, and the second beam set includes at least one planar beam.

[0031] The processor is configured to, for the (n+1)th frame of ultrasound image, generate a background image corresponding to the aforementioned ultrasound image based on the acquisition data of N focused beams corresponding to the (n+1)th frame, wherein the N focused beams are adjacent focused beams; and generate a foreground image corresponding to the aforementioned ultrasound image based on the acquisition data of Et planar beams corresponding to the aforementioned (n+1)th frame, wherein the Et planar beams are adjacent planar beams, and the first Et-N planar beams among the Et planar beams corresponding to the aforementioned (n+1)th frame are the last Et-N planar beams among the Et planar beams corresponding to the nth frame; wherein n, Et, and N are positive integers; and synthesize an ultrasound image of the corresponding frame based on the background image and foreground image corresponding to each frame of ultrasound image.

[0032] Fourthly, embodiments of this application also provide a computer-readable storage medium storing computer program instructions thereon, which, when executed by a processor, implement any of the steps described above in the ultrasound imaging method.

[0033] Fifthly, this application provides a computer program product comprising: computer program code, which, when executed on a computer, causes the computer to perform any of the steps described in the ultrasound imaging method.

[0034] Through the technical solutions in one or more of the above embodiments of this application, this application has at least the following technical effects:

[0035] In the embodiments provided in this application, when performing foreground imaging based on planar beams, the first Et-N planar beams of each frame's corresponding Et focused beams are the last Et-N planar beams of the Et planar beams corresponding to the previous frame. That is, when the foreground image of the next frame is imaged, it reuses the Et-N planar beams corresponding to the previous frame. When imaging in this way, the first planar beams of every two adjacent frames differ by N planar beams, where N is the number of focused beams corresponding to each frame of background image. At this time, the imaging frame rate of the ultrasound image depends entirely on N, the acquisition time of the focused beams no longer limits the acquisition time of the planar beams, and the foreground imaging frame rate is not limited by the frame packet length, resulting in a higher imaging frame rate for ultrasound imaging. Attached Figure Description

[0036] To more clearly illustrate the technical solutions of the embodiments of this application, the drawings used in the embodiments of this application will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0037] Figure 1 This is a schematic diagram of a traditional blood flow imaging timing technique in related technologies;

[0038] Figure 2 A schematic diagram of a conventional planar beam blood flow imaging timing provided for an embodiment of this application;

[0039] Figure 3 A schematic diagram illustrating an application scenario provided in an embodiment of this application;

[0040] Figure 4 A schematic diagram illustrating another application scenario provided by an embodiment of this application;

[0041] Figure 5 A schematic flowchart of an ultrasound imaging method provided in an embodiment of this application;

[0042] Figure 6 A schematic diagram of a focused beam and a planar beam transmission sequence provided for an embodiment of this application;

[0043] Figure 7 A schematic diagram of a focused beam and a planar beam transmission sequence provided for an embodiment of this application;

[0044] Figure 8 A schematic diagram of a focused beam and a planar beam transmission sequence provided for an embodiment of this application;

[0045] Figure 9 A schematic diagram of a focused beam and a planar beam transmission sequence provided for an embodiment of this application;

[0046] Figure 10 A schematic diagram of a focused beam and a planar beam transmission sequence provided for an embodiment of this application;

[0047] Figure 11 A schematic diagram of a focused beam and a planar beam transmission sequence provided for an embodiment of this application;

[0048] Figure 12 This is a schematic diagram of the structure of an ultrasound imaging device provided in an embodiment of this application;

[0049] Figure 13 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. Detailed Implementation

[0050] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. The described embodiments are only some, not all, of the embodiments of this application. All other embodiments obtained by those skilled in the art based on the embodiments of this application without creative effort are within the scope of protection of this application.

[0051] Furthermore, in the description of the embodiments of this application, unless otherwise stated, " / " and "÷" both mean division by, for example, P / Q and P÷Q can both mean P divided by Q; "×" and "*" both mean multiplication, for example, P*Q and P×Q can both mean P multiplied by Q.

[0052] Hereinafter, the terms "first" and "second" are used for descriptive purposes only and should not be construed as implying or suggesting relative importance or implicitly indicating the number of indicated technical features. Thus, a feature defined with "first" and "second" may explicitly or implicitly include one or more of that feature, and in the description of the embodiments of this application, unless otherwise stated, "multiple" means two or more.

[0053] To facilitate understanding of the ultrasound imaging method, device, and apparatus provided in the embodiments of this application, some terms used in the embodiments of this application will be explained below so that those skilled in the art can understand them.

[0054] (1) Frame rate (FR): The number of frames or images projected or displayed per second. Imaging frame rate is the number of images captured per second.

[0055] (2) Pulse Repetition Frequency (PRF): The number of pulses emitted per second, which is the reciprocal of the pulse repetition time, and is generally related to the imaging depth.

[0056] In traditional blood flow imaging, both the background grayscale image and the foreground blood flow image are acquired by line scanning using a focused beam. Figure 1 This is a schematic diagram of a traditional blood flow imaging timing sequence in related technologies, such as... Figure 1 As shown, B1, B2... represent the time sequence of background (grayscale) images, marked with dashed lines, meaning that B1, B2... each correspond to a frame of background image; C1, C2... represent the time sequence of foreground (blood flow) images, marked with solid lines, meaning that C1, C2... each correspond to a frame of foreground image.

[0057] Each background image is acquired using N scan lines, meaning each foreground image frame corresponds to N scan line regions. During the acquisition of each frame, N focused beams are emitted, each corresponding to a different scan line region. The acquisition sequence is defined as {b1, b2, ..., b...}. N} represents a focus beam, where each b corresponds to a focused beam.

[0058] Each foreground image is acquired using M scan lines, meaning each foreground image frame corresponds to M scan line regions. For each scan line, E1 focusing beams are emitted (i.e., frame packet length is E1). Therefore, during the acquisition of each frame, M×E1 focusing beams need to be emitted. Each pair of adjacent M focusing beams corresponds to a different scan line region, and their acquisition sequence is {c1, c2, ..., c...}. M×E1} represents a focused beam, where each c corresponds to a focused beam.

[0059] The overall image sequence follows the order of B1, C1, B2, C2… and so on.

[0060] At this point, the overall imaging frame rate is:

[0061] FR1=(N×PRF B +M×E1×PRF C ) -1 ,

[0062] Among them, PRF B and PRF C These are the pulse repetition frequencies of the background image and the foreground image, respectively.

[0063] Ultrasound plane wave imaging, as a novel imaging technique, offers several to tens of times higher data acquisition efficiency compared to traditional focused beam imaging, significantly improving the speed sensitivity and spatial resolution of blood flow imaging. However, because plane wave imaging lacks emission focusing capability, its performance in ultrasound grayscale images is inferior to that of traditional focused beam imaging. Therefore, to ensure image quality, in blood flow imaging, the foreground blood flow image is acquired using a plane wave, while the background grayscale image is acquired using a focused beam. When designing the acquisition timing of the plane wave, if the acquisition timing of the focused beam is adopted, the corresponding blood flow imaging timing is as follows: Figure 2 As shown.

[0064] like Figure 2 As shown, the background image is still acquired using a focused beam for line scanning, while the foreground image is acquired using a planar beam for frame scanning. Specifically, the timing corresponding to the focused beam is... Figure 1 Same, see also Figure 1Corresponding description. The foreground image timing sequence remains C1, C2…, marked with solid lines, meaning C1, C2… each correspond to one foreground image frame. For each foreground image frame, plane wave acquisition is performed using A transmission angles, with E2 transmissions at each angle (i.e., frame packet length is E2). That is, when acquiring each image frame, A×E2 plane wave beams need to be transmitted, with each adjacent A plane wave beam corresponding to a different transmission angle. Their acquisition timing sequence is defined as {c1, c2, …, c…}. A×E2} represents the overall image temporal sequence and Figure 1 same.

[0065] At this point, the overall imaging frame rate is

[0066] FR2=(N×PRF B +A×E2×PRF C ) -1 .

[0067] Since A is generally much smaller than M, when FR1 and FR2 are roughly equivalent, i.e., when M×E1≈A×E2, E2 is much larger than E1. This means that the performance of plane wave blood flow imaging is generally much greater than that of traditional blood flow imaging.

[0068] However, due to the fixed acquisition time of the background image, there is a trade-off between the overall imaging frame rate and the frame packet length. Therefore, for plane wave imaging, a frame packet length greater than 64 is generally desirable to obtain better imaging results, but according to... Figure 2 The image timing shown indicates that the acquisition time of the focusing beam limits the acquisition time of the planar beam, and the final imaging frame rate is generally below 20Hz (Hertz), which is difficult to meet the actual clinical needs.

[0069] Based on this, embodiments of this application provide an ultrasound diagnostic instrument, ultrasound imaging method, device, and medium, which are applied to ultrasound examinations of the human body. By combining two transmission modes, plane beam and focused beam, the acquisition sequences of foreground and background images are rearranged respectively, solving the time-occupancy problem of focused beam, making the foreground imaging frame rate not limited by the frame packet length, and improving the imaging frame rate of plane wave blood flow imaging.

[0070] It should be noted that, in the embodiments of this application, the foreground image is not limited to blood flow images, and the method provided in the embodiments of this application can also be applied to similar scenarios.

[0071] The following describes an application scenario of an optional ultrasound imaging method provided by an embodiment of this application, with reference to the accompanying drawings. For example... Figure 3 The ultrasound diagnostic instrument 30 shown includes a probe 301 and a processor 302, wherein:

[0072] The probe 301 is placed on the part of the human body to be diagnosed, i.e. the target area, during ultrasound diagnosis. It is used to respond to the ultrasound image generation command for the target area, alternately transmit the first beam set and the second beam set, and receive the acquisition data corresponding to each focused beam and the planar beam, and send the received acquisition data to the processor 302. The first beam set includes at least one focused beam, and the second beam set includes at least one planar beam.

[0073] Processor 302 is configured to, for the (n+1)th frame of ultrasound image, generate a background image corresponding to the aforementioned ultrasound image based on the acquisition data of N focused beams corresponding to the (n+1)th frame, wherein the N focused beams are adjacent focused beams; and generate a foreground image corresponding to the aforementioned ultrasound image based on the acquisition data of M planar beams corresponding to the aforementioned frame, wherein the M planar beams are adjacent planar beams, and the first MN planar beams of the M planar beams corresponding to the aforementioned frame are the last MN planar beams of the M planar beams corresponding to the nth frame; wherein n, M, and N are positive integers; and synthesize an ultrasound image of the corresponding frame based on the background image and foreground image corresponding to each frame of ultrasound image.

[0074] In some embodiments, the ultrasound diagnostic instrument may further include a display screen 303 for receiving each frame of ultrasound images sent by the processor 302 and displaying them in the corresponding display area.

[0075] In addition, this application embodiment also provides an optional application scenario for the ultrasound imaging method, such as... Figure 4 As shown, it includes an ultrasound device 40 and a server 41;

[0076] The ultrasound device 40 includes a display screen 401 and a probe 402;

[0077] An ultrasound device 40 is used to respond to an ultrasound image generation command for a target area. A probe 402 is placed in the target area of ​​the human body. The probe 402 alternately emits a first beam set and a second beam set, and receives the acquisition data corresponding to each focused beam and planar beam. The received acquisition data is sent to a server 41. The first beam set includes at least one focused beam, and the second beam set includes at least one planar beam. The device also receives each frame of ultrasound image sent by the server 41 and displays it on the corresponding display area of ​​the display screen 401.

[0078] Server 41 is configured to, for the (n+1)th frame of ultrasound image, generate a background image corresponding to the aforementioned ultrasound image based on the acquisition data of N focused beams corresponding to the (n+1)th frame, wherein the N focused beams are adjacent focused beams; and generate a foreground image corresponding to the aforementioned ultrasound image based on the acquisition data of M planar beams corresponding to the aforementioned frame, wherein the M planar beams are adjacent planar beams, and the first MN planar beams of the M planar beams corresponding to the aforementioned frame are the last MN planar beams of the M planar beams corresponding to the nth frame; wherein n, M, and N are positive integers; synthesize ultrasound images of corresponding frames based on the background image and foreground image corresponding to each frame of ultrasound image; and send each frame of ultrasound image to ultrasound device 40.

[0079] Of course, the methods provided in the embodiments of this application are not limited to... Figure 3 or Figure 4 The application scenarios shown can also be used in other possible application scenarios, and the embodiments of this application are not limited thereto.

[0080] like Figure 5 The diagram shows a flowchart of an ultrasound imaging method according to an embodiment of this application. The specific steps are as follows:

[0081] Step S501: In response to the command to generate an ultrasound image for the target area, the first beam set and the second beam set are transmitted alternately.

[0082] The first beam set includes at least one focused beam, and the second beam set includes at least one planar beam.

[0083] In some embodiments, the target region is a body region of a manually selected target object, such as the thyroid region or the heart region. When there is a need to generate an ultrasound image of the target region, an ultrasound image generation command can be sent to the device used to perform ultrasound imaging. In this embodiment, there are no restrictions on the way the command is sent; for example, the command can be sent by inputting a specific statement or clicking on a specific region.

[0084] After receiving the ultrasound image generation command, the system alternately transmits the first beam set and the second beam set, and receives the acquisition data corresponding to each transmitted beam (i.e., feedback data from the target area), so that a portion of the received acquisition data can be selected for image generation.

[0085] It should be noted that the number of beams included in the first beam set and the second beam combination in this application embodiment is not limited, and different numbers can be selected based on requirements in specific implementations. Furthermore, in this application embodiment, the number of beams included in the first or second beam set in adjacent transmissions can be exactly the same, have the same periodicity, or be different.

[0086] Step S502: For the (n+1)th frame of ultrasound image, based on the acquisition data of the N focused beams corresponding to the (n+1)th frame, generate a background image corresponding to the (n+1)th frame of ultrasound image; and based on the acquisition data of the Et planar beams corresponding to the (n+1)th frame, generate a foreground image corresponding to the (n+1)th frame of ultrasound image. The first Et-N planar beams in the Et planar beams corresponding to the (n+1)th frame are the last Et-N planar beams in the Et planar beams corresponding to the nth frame. n, N, and Et are positive integers.

[0087] Among them, the N focused beams corresponding to the (n+1)th frame are adjacent focused beams, and the Et planar beams corresponding to the (n+1)th frame are adjacent planar beams.

[0088] In some embodiments, when generating each frame of background image corresponding to the target region, the target region includes N scanning regions; when generating each frame of foreground image corresponding to the target region, the planar beam includes A emission angles, and each emission angle is emitted E2 times, where A and E2 are both positive integers.

[0089] In this embodiment, the values ​​of N, A, and E2 are not limited and can be set according to requirements. In some embodiments, to optimize imaging results, the value of A is usually set as large as possible to improve imaging results, provided that the performance of the ultrasound imaging system (data transmission efficiency, firmware and host computer memory, system computing efficiency, etc.) supports it.

[0090] At this time, when the first beam set and the second beam set are alternately transmitted, each adjacent N focused beams correspond to different scan line regions of the target area, and the background image corresponding to each frame of ultrasound image is generated based on the acquisition data corresponding to the adjacent N focused beams; each adjacent A planar beams correspond to different transmission angles, and the foreground image corresponding to each frame of ultrasound image is generated based on the acquisition data corresponding to the adjacent Et planar beams, where Et=A×E2.

[0091] In this embodiment, to ensure the subsequent beamforming calculation (generating the foreground image of the corresponding frame based on Et planar beams), it is necessary to ensure that the number of scan lines N and the emission angle A of the foreground planar beam are integer multiples of each other, i.e., N is an integer multiple of A. In some embodiments, the above beamforming calculation can be implemented using plane wave coherent compounding technology. Since the process of generating the background image based on the acquisition data of N focused beams and the foreground image based on the acquisition data of Et planar beams is prior art, it will not be described in detail here.

[0092] In some embodiments, for the first frame of ultrasound image, a background image corresponding to the first frame of ultrasound image is generated based on the acquisition data of N focused beams corresponding to the first frame; and a foreground image corresponding to the first frame of ultrasound image is generated based on the acquisition data of Et planar beams corresponding to the first frame.

[0093] Step S503: Based on the background image and foreground image corresponding to each frame of ultrasound image, synthesize the ultrasound image of the corresponding frame.

[0094] The above method uses both plane waves and focused beams to take into account the quality of both the foreground and background in ultrasound imaging; and rearranges the acquisition sequence of the foreground and background images so that the blood flow imaging frame rate is not limited by the frame packet length.

[0095] It should be noted that the ultrasound imaging method described in steps S501-S503 of this application embodiment is designed for general scenarios where Et is much greater than N, i.e., the minimum value of E2 is N / A. When the values ​​of Et and N are small, equal, or less than N, E2 can be appropriately increased, or N can be reduced using multi-line acquisition (MLA) technology, so that the relationship between Et and N is much greater than N. In specific implementations, the degree of "much greater than" can be set manually, for example, setting Et to be ten times greater than N as Et is much greater than N, or setting Et to be one hundred times greater than N as Et is much greater than N, etc.

[0096] For most clinical applications, setting N=80 and A=5 can meet the basic requirements of plane wave blood flow imaging. The maximum sampling frame (PRF) of the foreground image is used. B =PRF C Based on calculations, for areas with shallow imaging depth such as the thyroid and breast, N=140 and A=7 can be set, with a theoretical imaging frame rate of approximately 68.7Hz at an imaging depth of 4cm; for abdominal areas such as the liver and kidneys, N=140 and A=5 can be set, with a theoretical imaging frame rate of approximately 27.5Hz at an imaging depth of 10cm; for the heart, N=90 and A=3 or 5 can be set, with a theoretical imaging frame rate of approximately 28.5Hz at an imaging depth of 15cm.

[0097] The following combination Figure 6-11 The above-mentioned ultrasound imaging method will be explained in detail with specific examples.

[0098] In some embodiments, if each first beam set includes a focused beam and each second beam set includes a planar beam, then in step S502 above: the N focused beams corresponding to the (n+1)th frame are the focused beams included in the N×n+1 to N×(n+1)th first beam sets; the Et planar beams corresponding to the (n+1)th frame are the planar beams included in the N×n+1 to N×n+Etth second beam sets.

[0099] Figure 6 This demonstrates one possible combination of background and foreground images for each pair. Figure 6 In the diagram, B1, B2... represent the background image sequence, marked with a dashed line box, meaning that B1, B2... each correspond to a frame of background image; C1, C2... represent the foreground image sequence, marked with a solid line box, meaning that C1, C2... each correspond to a frame of foreground image.

[0100] like Figure 6 As shown, N represents the total number of focused beams (each focused beam corresponds to a scan line area) required for each frame of the background image. Each frame of the background image corresponds to N focused beams, i.e., B1, B2, ... correspond to N focused beams (represented by b in the figure). Since each first beam set includes one focused beam, one b is equivalent to one first beam set. In this case, the N focused beams corresponding to the (n+1)th frame are: the focused beams included in the N×n+1 to N×(n+1)th first beam sets; for example, B1 corresponds to {b1, b2, ..., b...} N}、B2 corresponds to {b N+1 ,b N+2 ,…,b 2N}、B3 corresponds to {b 2N+1 ,b 2N+2 ,…,b 3N}wait.

[0101] Et represents the total number of planar beams required for each frame of the foreground image. Each frame of the foreground image corresponds to Et planar beams, i.e., C1, C2, ... correspond to Et planar beams (represented by c in the diagram). Since each second beam set includes one planar beam, one c is equivalent to one second beam set. Therefore, the Et planar beams corresponding to the (n+1)th frame are the planar beams included in the N×n+1 to N×n+Et second beam sets; for example, C1 corresponds to {c1, c2, ..., c...} Et}、C2 corresponds to {c N+1 ,c N+2 ,…,c N+Et}、C3 corresponds to {c 2N+1 ,c 2N+2 ,…,c 2N+Et}wait.

[0102] The overall image acquisition sequence is in the order of b1, c1, b2, c2... and so on.

[0103] At this point, the overall imaging frame rate is:

[0104] FR3=(N×(PRF B +PRF C )) -1 .

[0105] Among them, PRF B and PRF C These are the pulse repetition frequencies of the background image and the foreground image, respectively.

[0106] and Figure 1 and Figure 2 Compared to the related technologies shown, Figure 6 The transmission timing of the focused beam and the planar beam shown in the figure has an overall imaging frame rate determined only by the frame rate of the background image, and is not affected by the frame packet length E2 of the planar beam or the number of transmission angles A of the planar beam. This solves the trade-off between frame packet length and imaging frame rate, and enables the overall imaging to have a higher imaging frame rate.

[0107] In some embodiments, for scenarios where Et is much greater than N, such as ultrasound super-resolution imaging or ultrasound localization microscopy (ULM) imaging technology, Et is generally in the range of thousands to tens of thousands. In this case, each first beam set can be set to include one focused beam, and each second beam set can include A planar beams. Then, in step S502 above: the N focused beams corresponding to the (n+1)th frame are the focused beams included in the N×n+1 to N×(n+1)th first beam sets; the Et planar beams corresponding to the (n+1)th frame are the planar beams included in the N×n+1 to N×n+Et / Ath second beam sets.

[0108] Figure 7 This demonstrates one possible combination of background and foreground images for each pair. Figure 7 In the diagram, B1, B2... represent the background image sequence, marked with a dashed line box, meaning that B1, B2... each correspond to a frame of background image; C1, C2... represent the foreground image sequence, marked with a solid line box, meaning that C1, C2... each correspond to a frame of foreground image.

[0109] like Figure 7As shown, N represents the total number of focused beams (each focused beam corresponds to a scan line area) required for each frame of the background image. Each frame of the background image corresponds to N focused beams, i.e., B1, B2, ... correspond to N focused beams (represented by b in the figure). Since each first beam set includes one focused beam, one b is equivalent to one first beam set. In this case, the N focused beams corresponding to the (n+1)th frame are: the focused beams included in the N×n+1 to N×(n+1)th first beam sets; for example, B1 corresponds to {b1, b2, ..., b...} N}、B2 corresponds to {b N+1 ,b N+2 ,…,b 2N}wait.

[0110] Et represents the total number of planar beams required for each frame of the foreground image. Each frame of the foreground image corresponds to Et planar beams, i.e., C1, C2… correspond to Et planar beams (represented by c in the diagram). Since each second beam set includes A planar beams, A c are equivalent to one second beam set. Therefore, the Et planar beams corresponding to the (n+1)th frame are the planar beams included in the N×n+1 to N×n+Et / A second beam sets, i.e., each frame corresponds to Et / A (i.e., E2) second beam sets. For example, C1 corresponds to {c1, c2, …, c…} Et}, which includes the first to E2 second beam sets; C2 corresponds to {c A×N+1 ,c A×N+2 ,…,c A×N+Et This includes the N+1 to N+E2 second beam sets.

[0111] The overall image acquisition sequence is as follows: b1, {c1, c2, ..., c A}、b2、{c A+1 ,c A+2 ,…,c 2A The order of}, b3, etc., continues in this manner.

[0112] In some embodiments, if each first beam set includes k focused beams and each second beam set includes one planar beam, where k is a positive integer and N is a multiple of k, then in step S502 above: the N focused beams corresponding to the (n+1)th frame are the focused beams included in the (n×N / k+1)th to (n+1)×N / kth first beam sets; the Et planar beams corresponding to the (n+1)th frame are the planar beams included in the (n×N / k+1)th to (n×N / k+Et)th second beam sets. It should be noted that the specific value of k is not limited in this embodiment and can be set based on requirements.

[0113] Figure 8This demonstrates one possible combination of background and foreground images for each pair. Figure 8 In the diagram, B1, B2... represent the background image sequence, marked with a dashed line box, meaning that B1, B2... each correspond to a frame of background image; C1, C2... represent the foreground image sequence, marked with a solid line box, meaning that C1, C2... each correspond to a frame of foreground image.

[0114] like Figure 8 As shown, N represents the total number of focused beams (each focused beam corresponds to a scan line area) required for each frame of the background image. Each frame of the background image corresponds to N focused beams, i.e., B1, B2, ... correspond to N focused beams (represented by b in the figure). Since each first beam set includes k focused beams, k b are equivalent to one first beam set. At this time, the N focused beams corresponding to the (n+1)th frame are: the focused beams included in the (n×N / k+1)th to (n+1)×N / kth first beam sets; for example, B1 corresponds to {b1, b2, ..., b...} N}, which includes the first to N / k first beam sets; B2 corresponds to {b N+1 ,b N+2 ,…,b 2N This includes the N / k+1 to 2N / k first beam sets.

[0115] Et represents the total number of planar beams required for each frame of the foreground image. Each frame of the foreground image corresponds to Et planar beams, i.e., C1, C2, ... correspond to Et planar beams (represented by c in the diagram). Since each second beam set includes one planar beam, one c is equivalent to one second beam set. Therefore, the Et planar beams corresponding to the (n+1)th frame are the planar beams included in the second beam sets from the (n×N / k+1)th to the (n×N / k+Et)th; for example, C1 corresponds to {c1, c2, ..., c...} Et}、C2 corresponds to {c N / k+1 ,c N / k+2 ,…,c N / k+Et}wait.

[0116] The overall image acquisition sequence is as follows: {b1, b2, ..., b k}、c1、{b k+1 ,b k+2 ,…,b 2k The order of}, c2, etc., continues.

[0117] In some embodiments, when the first beam set and the second beam set are alternately transmitted as described in this application, after transmitting any second beam set, the first beam set is transmitted after an interval corresponding to a preset idle time period. The preset idle time period is called the idle time p.

[0118] It should be noted that the preset idle time for each second beam set can be the same or different.

[0119] Figure 9 This indicates a combination of background and foreground images for each pair, with B1 ranging from b1 to b N Composed of, B2 is made up of b N+1 To b 2N Composition, and so on; C1 from c1 to c Et Composition, C2 is composed of c N+1 To c N+Et Composition, and so on.

[0120] Figure 9 Based on Figure 6 A variant that can be used to adjust PRF C In this scenario, after the data acquisition timings c1, c2, ..., idle periods p1, p2, ... are added, marked with diagonal lines. By uniformly adjusting these idle periods, the PRF (Predicted Regression Factor) can be changed. C To measure blood flow velocity at different scales. The overall acquisition sequence follows the alternating order of background image, foreground image, and idle time, i.e., b1, c1, p1, b2, c2, p2... and so on.

[0121] The idle times p1, p2... can also be non-fixed values; for example, they can be set as {p1=p3=p5=...=p...}. odd p2 = p4 = p6 = ... p even}, where odd and even represent odd and even numbers respectively, meaning that two PRFs are set in the same imaging sequence. C This is used to address the velocity ambiguity problem in blood flow imaging. Similarly, multiple PRFs can be set within the same imaging sequence. C To meet various measurement needs.

[0122] Figure 10 This indicates a combination of background and foreground images for each pair, with B1 ranging from b1 to b N Composed of, B2 is made up of b N+1 To b 2N Composition, and so on; C1 from c1 to c Et Composition, C2 is composed of c A×N+1 To c A×N+Et Composition, and so on.

[0123] Figure 10 Based on Figure 7A variation of this approach can be used in scenarios where Et is much greater than N, such as ultrasound super-resolution or ultrasound localization microscopy (ULM) imaging techniques, where Et is typically in the thousands to tens of thousands. The overall acquisition sequence is based on b1, {c1,c2,…,c…} A}、p1、b2、{c A+1 ,c A+2 ,…,c 2A The order of p1, p2, etc., continues. Idle times p1, p2, etc., are arbitrarily adjustable, allowing for the setting of multiple PRFs within the same imaging sequence. C .

[0124] Figure 11 This indicates a combination of background and foreground images for each pair, with B1 ranging from b1 to b N Composed of, B2 is made up of b N+1 To b 2N Composition, and so on; C1 from c1 to c Et Composition, C2 is composed of c N / k+1 To c N / k+Et Composition, and so on.

[0125] Figure 11 Based on Figure 8 A variation where the overall acquisition timing is in the order of {b1, b2, ..., b k}、c1、p1、{b k+1 ,b k+2 ,…,b 2k The order is p1, p2, p2… and so on. Idle times p1, p2… are arbitrarily adjustable, allowing multiple PRFs to be set within the same imaging sequence. C Provided that N and A are integer multiples of each other, and N is an integer multiple of k, k can also be arbitrarily adjusted.

[0126] Based on the same inventive concept, such as Figure 12 As shown, this application provides an ultrasound imaging device 1200, which can be specifically applied to the ultrasound diagnostic instrument in the above embodiments, including:

[0127] The transmitting module 1201 is configured to alternately transmit a first beam set and a second beam set in response to an ultrasound image generation command for a target area; the first beam set includes at least one focused beam, and the second beam set includes at least one planar beam;

[0128] The generation module 1202 is configured to generate a background image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of N focused beams corresponding to the (n+1)th frame, wherein the N focused beams are adjacent focused beams; and to generate a foreground image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of Et planar beams corresponding to the (n+1)th frame, wherein the Et planar beams are adjacent planar beams, and the first Et-N planar beams of the Et planar beams corresponding to the (n+1)th frame are the last Et-N planar beams of the Et planar beams corresponding to the nth frame; wherein n, Et, and N are positive integers.

[0129] The synthesis module 1203 is used to synthesize ultrasound images of corresponding frames based on the background and foreground images corresponding to each frame of ultrasound images.

[0130] Optionally, each of the N adjacent focused beams corresponds to a different scan line region of the target area;

[0131] Each of the adjacent A planar beams corresponds to a different transmission angle;

[0132] Where A is a positive integer, and Et and N are multiples of A.

[0133] Optionally, if each first beam set includes a focused beam and each second beam set includes a planar beam, then:

[0134] The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame;

[0135] The Et planar beams corresponding to the (n+1)th frame are the planar beams included in the second beam sets from the (N×n+1)th to the (N×n+Et)th.

[0136] Optionally, if each first beam set includes a focused beam and each second beam set includes A planar beams, then:

[0137] The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame;

[0138] The Et planar beam corresponding to the (n+1)th frame is the planar beam included in the second beam set from the N×n+1th to the N×n+Et / Ath.

[0139] Optionally, if each first beam set includes k focused beams, and each second beam set includes one planar beam, where k is a positive integer and N is a multiple of k, then:

[0140] The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the N×n / k+1th to the N×(n+1) / kth frame;

[0141] The Et planar beam corresponding to the (n+1)th frame is the planar beam included in the second beam set from the N×n / k+1th to the N×n / k+Etth.

[0142] Optionally, the aforementioned transmitting module 1201 is also used for:

[0143] After transmitting any of the second beam sets, the first beam set is transmitted after a preset idle time corresponding to any of the second beam sets.

[0144] Optionally, the above-mentioned generation module 1202 is also used for:

[0145] For the first frame of ultrasound image, a background image corresponding to the first frame of ultrasound image is generated based on the acquisition data of N focused beams corresponding to the first frame; and a foreground image corresponding to the first frame of ultrasound image is generated based on the acquisition data of Et planar beams corresponding to the first frame.

[0146] It should be noted that the module division in the embodiments of this application is illustrative and only represents one logical functional division. In actual implementation, there may be other division methods. Furthermore, the functional modules in the various embodiments of this application can be integrated into one processing module, or each module can exist physically separately, or two or more modules can be integrated into one module. The integrated modules described above can be implemented in hardware or as software functional modules.

[0147] If the integrated module is implemented as a software functional module and sold or used as an independent product, it can be stored in a processor-readable storage medium. Based on this understanding, the technical solution of this application, in essence, 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.

[0148] It should be noted that the apparatus provided in this embodiment of the invention can implement all the method steps implemented in the above method embodiment and can achieve the same technical effect. Therefore, the parts and beneficial effects that are the same as those in the method embodiment will not be described in detail here.

[0149] Based on the same inventive concept, this application provides an electronic device that can realize the ultrasound imaging function described above. Please refer to... Figure 13The device includes at least one processor 1301, a memory 1302 connected to the at least one processor, and a probe 1303. In this embodiment, the specific connection medium between the processor 1301 and the memory 1302 is not limited. Figure 13 The processor 1301 and memory 1302 can be connected via a bus. The bus can be divided into address bus, data bus, control bus, etc. For ease of representation, Figure 13 The bus is represented by only one line, but this does not mean that there is only one bus or one type of bus.

[0150] The processor 1301 is the control center of the electronic device, capable of connecting various parts of the device via various interfaces and lines. It performs data processing by running or executing instructions stored in the memory 1302 and accessing data stored in the memory 1302. Optionally, the processor 1301 may include one or more processing units. The processor 1301 may integrate an application processor and a modem processor. The application processor primarily handles the operating system, user interface, and applications, while the modem processor primarily handles issuing instructions. It is understood that the modem processor may not be integrated into the processor 1301. In some embodiments, the processor 1301 and the memory 1302 may be implemented on the same chip; in other embodiments, they may be implemented on separate chips.

[0151] Processor 1301 can be a general-purpose processor, such as a central processing unit (CPU), digital signal processor, application-specific integrated circuit (ASIC), field-programmable gate array (FPGA), or other programmable logic device, discrete gate or transistor logic device, or discrete hardware component, capable of implementing or executing the methods, steps, and logic block diagrams disclosed in the embodiments of this application. The general-purpose processor can be a microprocessor or any conventional processor. The steps of the methods disclosed in the embodiments of the test data generation method can be directly manifested as being executed by a hardware processor, or executed by a combination of hardware and software modules within the processor.

[0152] Memory 1302, as a non-volatile computer-readable storage medium, can be used to store non-volatile software programs, non-volatile computer-executable programs, and modules. Memory 1302 may include at least one type of storage medium, such as flash memory, hard disk, multimedia card, card-type memory, random access memory (RAM), static random access memory (SRAM), programmable read-only memory (PROM), read-only memory (ROM), electrically erasable programmable read-only memory (EEPROM), magnetic storage, magnetic disk, optical disk, etc. Memory 1302 can be any other medium capable of carrying or storing desired program code in the form of instructions or data structures that can be accessed by a computer, but is not limited thereto. In the embodiments of this application, memory 1302 may also be a circuit or any other device capable of implementing storage functions for storing program instructions and / or data.

[0153] In this embodiment, the memory 1302 stores a computer program, which, when executed by the processor 1301, implements the above-described ultrasound imaging method.

[0154] Those skilled in the art will understand that embodiments of this application can be provided as methods, systems, or computer program products. Therefore, this application can take the form of a completely hardware embodiment, a completely software embodiment, or an embodiment combining software and hardware aspects. Furthermore, this application can take the form of a computer program product embodied on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0155] This application is described with reference to flowchart illustrations and / or block diagrams of methods, apparatus (systems), and computer program products according to this application. It should be understood that each block of the flowchart illustrations and / or block diagrams, and combinations of blocks in the flowchart illustrations and / or block diagrams, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, special-purpose computer, embedded processor, or other programmable data processing apparatus to produce a machine, such that the instructions, which execute via the processor of the computer or other programmable data processing apparatus, generate instructions for implementing the flowchart illustrations. Figure 1 One or more processes and / or boxes Figure 1 A device that provides the functions specified in one or more boxes.

[0156] These computer program instructions may also be stored in a computer-readable storage medium that can direct a computer or other programmable data processing device to function in a particular manner, such that the instructions stored in the computer-readable storage medium produce an article of manufacture including instruction means, which are implemented in a process Figure 1 One or more processes and / or boxes Figure 1 The function specified in one or more boxes.

[0157] These computer program instructions may also be loaded onto a computer or other programmable data processing equipment to cause a series of operational steps to be performed on the computer or other programmable equipment to produce a computer-implemented process, thereby providing instructions that execute on the computer or other programmable equipment for implementing the process. Figure 1 One or more processes and / or boxes Figure 1 The steps of the function specified in one or more boxes.

[0158] Obviously, those skilled in the art can make various modifications and variations to this application without departing from the spirit and scope of this application. Therefore, if such modifications and variations fall within the scope of the claims of this application and their equivalents, this application also intends to include such modifications and variations.

Claims

1. An ultrasonic diagnostic instrument, characterized by, Including the probe and processor; The probe is used to be placed in a target area of ​​the human body and, in response to an ultrasound image generation command for the target area, alternately emits a first beam set and a second beam set; the first beam set includes at least one focused beam, and the second beam set includes at least one planar beam; The processor is configured to, for the (n+1)th frame of ultrasound image, generate a background image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of N focused beams corresponding to the (n+1)th frame, wherein the N focused beams are adjacent focused beams; and generate a foreground image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of Et planar beams corresponding to the (n+1)th frame, wherein the Et planar beams are adjacent planar beams, and the first Et-N planar beams of the Et planar beams corresponding to the (n+1)th frame are the last Et-N planar beams of the Et planar beams corresponding to the nth frame, and the last N planar beams of the Et planar beams corresponding to the (n+1)th frame are the N planar beams returned by the planar beams transmitted corresponding to the (n+1)th frame; wherein n, Et, and N are positive integers; and synthesize ultrasound images of corresponding frames based on the background image and foreground image corresponding to each frame of ultrasound image; Each pair of N adjacent focused beams corresponds to a different scan line region of the target area; Each of the adjacent A planar beams corresponds to a different transmission angle; Where A is a positive integer, and Et and N are multiples of A; If each first beam set includes a focused beam, and each second beam set includes a planar beam, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame; The Et planar beams corresponding to the (n+1)th frame are: the planar beams included in the N×n+1 to N×n+Et second beam sets; or If each first beam set includes one focused beam, and each second beam set includes A planar beams, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame; The Et planar beam corresponding to the (n+1)th frame is: the planar beams included in the second beam set from the N×n+1th to the N×n+Et / Ath frame; or If each first beam set includes k focused beams, and each second beam set includes one planar beam, where k is a positive integer and N is a multiple of k, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the N×n / k+1th to the N×(n+1) / kth frame; The Et planar beam corresponding to the (n+1)th frame is the planar beam included in the second beam set from the N×n / k+1th to the N×n / k+Etth.

2. The ultrasound diagnostic instrument as described in claim 1, characterized in that, The probe is also used for: After transmitting any of the second beam sets, after a preset idle time corresponding to any of the second beam sets, the first beam set is transmitted.

3. The ultrasound diagnostic instrument as described in claim 1, characterized in that, The processor is also used for: For the first frame of ultrasound image, a background image corresponding to the first frame of ultrasound image is generated based on the acquisition data of N focused beams corresponding to the first frame; Based on the acquisition data of Et planar beams corresponding to the first frame, a foreground image corresponding to the first frame ultrasound image is generated; based on the background image and foreground image corresponding to the first frame ultrasound image, the first frame ultrasound image is synthesized.

4. An ultrasound imaging method, characterized in that, The method includes: In response to an instruction to generate an ultrasound image for a target region, a first beam set and a second beam set are alternately transmitted; the first beam set includes at least one focused beam, and the second beam set includes at least one planar beam; For the (n+1)th frame of ultrasound image, a background image corresponding to the (n+1)th frame of ultrasound image is generated based on the acquisition data of N focused beams corresponding to the (n+1)th frame, where the N focused beams are adjacent focused beams; and a foreground image corresponding to the (n+1)th frame of ultrasound image is generated based on the acquisition data of Et planar beams corresponding to the (n+1)th frame, where the Et planar beams are adjacent planar beams, and the first Et-N planar beams of the Et planar beams corresponding to the (n+1)th frame are the last Et-N planar beams of the Et planar beams corresponding to the nth frame, and the last N planar beams of the Et planar beams corresponding to the (n+1)th frame are the N planar beams returned by the planar beams transmitted corresponding to the (n+1)th frame; where n, Et, and N are positive integers; each adjacent N focused beams correspond to different scan line regions of the target area; Each of the adjacent A planar beams corresponds to a different transmission angle; Where A is a positive integer, and Et and N are multiples of A; Based on the background and foreground images corresponding to each frame of ultrasound image, the ultrasound image of the corresponding frame is synthesized. If each first beam set includes a focused beam, and each second beam set includes a planar beam, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame; The Et planar beams corresponding to the (n+1)th frame are: the planar beams included in the N×n+1 to N×n+Et second beam sets; or If each first beam set includes one focused beam, and each second beam set includes A planar beams, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame; The Et planar beam corresponding to the (n+1)th frame is: the planar beams included in the second beam set from the N×n+1th to the N×n+Et / Ath frame; or If each first beam set includes k focused beams, and each second beam set includes one planar beam, where k is a positive integer and N is a multiple of k, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the N×n / k+1th to the N×(n+1) / kth frame; The Et planar beam corresponding to the (n+1)th frame is the planar beam included in the second beam set from the N×n / k+1th to the N×n / k+Etth.

5. An ultrasonic imaging device, characterized in that, The device includes: The transmitting module is configured to alternately transmit a first beam set and a second beam set in response to an ultrasound image generation command for a target area; the first beam set includes at least one focused beam, and the second beam set includes at least one planar beam; A generation module is used to generate a background image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of N focused beams corresponding to the (n+1)th frame, wherein the N focused beams are adjacent focused beams; and to generate a foreground image corresponding to the (n+1)th frame of ultrasound image based on the acquisition data of Et planar beams corresponding to the (n+1)th frame, wherein the Et planar beams are adjacent planar beams, and the first Et-N planar beams of the Et planar beams corresponding to the (n+1)th frame are the last Et-N planar beams of the Et planar beams corresponding to the nth frame, and the last N planar beams of the Et planar beams corresponding to the (n+1)th frame are the N planar beams returned by the planar beams transmitted corresponding to the (n+1)th frame; wherein n, Et, and N are positive integers; wherein n, Et, and N are positive integers; each adjacent N focused beams correspond to different scan line regions of the target area; Each of the adjacent A planar beams corresponds to a different transmission angle; Where A is a positive integer, and Et and N are multiples of A; The synthesis module is used to synthesize ultrasound images of corresponding frames based on the background and foreground images corresponding to each frame of ultrasound image; If each first beam set includes a focused beam, and each second beam set includes a planar beam, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame; The Et planar beams corresponding to the (n+1)th frame are: the planar beams included in the N×n+1 to N×n+Et second beam sets; or If each first beam set includes one focused beam, and each second beam set includes A planar beams, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the (N×n+1)th to the (N×(n+1)th)th frame; The Et planar beam corresponding to the (n+1)th frame is: the planar beams included in the second beam set from the N×n+1th to the N×n+Et / Ath frame; or If each first beam set includes k focused beams, and each second beam set includes one planar beam, where k is a positive integer and N is a multiple of k, then: The N focused beams corresponding to the (n+1)th frame are: the focused beams included in the first beam set from the N×n / k+1th to the N×(n+1) / kth frame; The Et planar beam corresponding to the (n+1)th frame is the planar beam included in the second beam set from the N×n / k+1th to the N×n / k+Etth.

6. A computer-readable storage medium having computer program instructions stored thereon, characterized in that, When the computer program instructions are executed by the processor, they implement the steps of the method of claim 4.

Images