Ultrasonic diagnostic instrument, ultrasonic imaging method and device and medium

Abstract

The invention 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 collection sequences of focused beams and planar beams so that a foreground imaging frame frequency is not limited by a frame packet length. The method comprises the following steps: in response to an ultrasonic image generation instruction, alternately transmitting a first beam set and a second beam set; generating a background image of the (n + 1) th frame based on the acquired data of the N focusing beams corresponding to the (n + 1) th frame; on the basis of the acquired data of the Et planar beams corresponding to the (n + 1) th frame, generating the foreground image of the (n + 1) th frame and the front (Et-N) planar beams in the Et planar beams corresponding to the (n + 1) th frame, namely the rear (Et-N) planar beams in the Et planar beams corresponding to the nth frame; wherein n, Et and N are positive integers; and based on the background image and the foreground image corresponding to each frame of ultrasonic image, synthesizing the corresponding frame of ultrasonic image.

Description

Technical Field

[0001] The present application relates to the field of ultrasonic imaging technology, and in particular to an ultrasonic diagnostic instrument, an ultrasonic imaging method, a device and a medium. Background Art

[0002] Ultrasonic plane wave imaging is a new imaging technology that is implemented by simultaneously stimulating all transducers on the transmitting aperture, so that the probe emits sound waves with plane wave characteristics, covering the entire imaging area in a single emission. Therefore, compared with traditional focused beams, the data acquisition efficiency of plane wave imaging has increased by several to dozens of times, which can greatly improve the speed sensitivity and spatial resolution of blood flow imaging.

[0003] However, since plane wave imaging does not have the ability to focus transmission, its performance on ultrasound grayscale images is poorer than that of traditional focused beams. To ensure image quality, when implementing 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 emission modes of the plane beam and the focused beam are different. When designing the acquisition timing of the plane beam, if the acquisition timing of the focused beam is used, the acquisition time of the focused beam will limit the acquisition time of the plane beam, thereby limiting the frame packet (Ensemble) length of blood flow imaging, ultimately resulting in limited performance improvement of blood flow imaging. Summary of the invention

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

[0006] In a first aspect, an embodiment of the present application provides an ultrasonic imaging method, the method comprising:

[0007] In response to an instruction for generating an ultrasound image of a target area, 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+1th frame of ultrasound image, based on the acquisition data of the N focused beams corresponding to the n+1th frame, a background image corresponding to the n+1th frame of ultrasound image is generated, and the N focused beams are adjacent focused beams; and based on the acquisition data of the Et plane beams corresponding to the n+1th frame, a foreground image corresponding to the n+1th frame of ultrasound image is generated, and the Et plane beams are adjacent plane beams, and the first Et-N plane beams among the Et plane beams corresponding to the n+1th frame are the last Et-N plane beams among the Et plane beams corresponding to the nth frame; wherein n, Et and N are positive integers;

[0009] Based on the background image and the foreground image corresponding to each frame of the ultrasonic image, the ultrasonic image of the corresponding frame is synthesized.

[0010] In some possible implementations, each of the N adjacent focused beams corresponds to a different scan line area of ​​the target area; each of the A adjacent plane beams corresponds to a different emission angle;

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

[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+1th frame are: the focused beams included in the N×n+1th to N×(n+1)th first beam sets;

[0014] The Et plane beams corresponding to the above-mentioned n+1th frame are: the plane beams included in the N×n+1th to N×n+Etth 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+1th frame are: the focused beams included in the N×n+1th to N×(n+1)th first beam sets;

[0017] The Et plane beams corresponding to the above-mentioned n+1th frame are: the plane beams included in the N×n+1th to N×n+Et / Ath second beam sets.

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

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

[0020] The Et plane beams corresponding to the above-mentioned n+1th frame are: the plane beams included in the N×n / k+1th to N×n / k+Etth second beam sets.

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

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

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

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

[0025] In a second aspect, an embodiment of the present application further provides an ultrasonic imaging device, the device comprising:

[0026] A transmitting module, configured to alternately transmit a first beam set and a second beam set in response to an instruction for generating an ultrasound image of 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] A generation module is used to generate, for the n+1th frame of ultrasound image, a background image corresponding to the n+1th frame of ultrasound image based on the acquisition data of N focused beams corresponding to the n+1th frame, wherein the N focused beams are adjacent focused beams; and to generate, based on the acquisition data of Et plane beams corresponding to the n+1th frame, a foreground image corresponding to the n+1th frame of ultrasound image, wherein the Et plane beams are adjacent plane beams, and the first Et-N plane beams among the Et plane beams corresponding to the n+1th frame are the last Et-N plane beams among the Et plane beams corresponding to the nth frame; wherein n, Et and N are positive integers; wherein n, Et and N are positive integers;

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

[0029] In a third aspect, an embodiment of the present application further provides an ultrasonic diagnostic instrument, including a probe and a processor;

[0030] A probe is used to be placed in a target area of ​​a human body, and in response to an instruction for generating an ultrasound image of the target area, alternately transmit 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] A processor is used to generate, for an n+1th frame of ultrasonic image, a background image corresponding to the above-mentioned n+1th frame of ultrasonic image based on the acquisition data of N focused beams corresponding to the n+1th frame, wherein the above-mentioned N focused beams are adjacent focused beams; and to generate a foreground image corresponding to the above-mentioned n+1th frame of ultrasonic image based on the acquisition data of Et plane beams corresponding to the n+1th frame, wherein the above-mentioned Et plane beams are adjacent plane beams, and the first Et-N plane beams among the Et plane beams corresponding to the above-mentioned n+1th frame are the last Et-N plane beams among the Et plane beams corresponding to the nth frame; wherein n, Et and N are positive integers; and based on the background image and foreground image corresponding to each frame of ultrasonic image, synthesize the ultrasonic image of the corresponding frame.

[0032] In a fourth aspect, an embodiment of the present application further provides a computer-readable storage medium having computer program instructions stored thereon, which, when executed by a processor, implement any of the above steps in the above-mentioned ultrasound imaging method.

[0033] In a fifth aspect, the present application provides a computer program product, which includes: a computer program code, which, when executed on a computer, enables the computer to execute any one of the above steps in the above ultrasound imaging method.

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

[0035] In the embodiment provided in the present application, when foreground imaging is performed based on plane beams, the first Et-N plane beams of the Et focused beams corresponding to each frame are the last Et-N plane beams of the Et plane beams corresponding to the previous frame, that is, when imaging the foreground image of the next frame, the Et-N plane beams corresponding to the previous frame are reused. When imaging is performed in this way, the first plane beams corresponding to each two adjacent frames differ by N plane beams, and N is the number of focused beams corresponding to each frame of the background image. At this time, the imaging frame rate of the ultrasonic image depends entirely on N, and the acquisition time of the focused beam will no longer limit the acquisition time of the plane beam. The foreground imaging frame rate is also not limited by the frame packet length, and the ultrasonic imaging has a higher imaging frame rate. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required for use in the embodiments of the present application will be briefly introduced below. Obviously, the drawings introduced below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0037] Figure 1 A schematic diagram of a conventional blood flow imaging timing sequence in the related art;

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

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

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

[0041] Figure 5 A schematic diagram of a flow chart of an ultrasonic imaging method provided in an embodiment of the present application;

[0042] Figure 6 A schematic diagram of a focused beam and a plane beam transmission sequence provided in an embodiment of the present application;

[0043] Figure 7 A schematic diagram of a focused beam and a plane beam transmission sequence provided in an embodiment of the present application;

[0044] Figure 8 A schematic diagram of a focused beam and a plane beam transmission sequence provided in an embodiment of the present application;

[0045] Fig. 9 A schematic diagram of a focused beam and a plane beam transmission sequence provided in an embodiment of the present application;

[0046] Fig.10 A schematic diagram of a focused beam and a plane beam transmission sequence provided in an embodiment of the present application;

[0047] Fig.11 A schematic diagram of a focused beam and a plane beam transmission sequence provided in an embodiment of the present application;

[0048] Fig.12 A schematic diagram of the structure of an ultrasonic imaging device provided in an embodiment of the present application;

[0049] Fig.13 A schematic diagram of the structure of an electronic device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0050] In order to make the purpose, technical scheme and advantages of the embodiments of the present application clearer, the technical scheme in the embodiments of the present application will be clearly and completely described below in conjunction with the drawings in the embodiments of the present application. Among them, the described embodiments are part of the embodiments of the present application, rather than all the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of this application.

[0051] Furthermore, in the description of the embodiments of the present application, unless otherwise specified, “ / ” and “÷” both mean division, for example, P / Q and P÷Q both mean P divided by Q; “×” and “*” both mean multiplication, for example, P*Q and P×Q both mean P multiplied by Q.

[0052] In the following, the terms "first" and "second" are used for descriptive purposes only and should not be understood as suggesting or implying relative importance or implicitly indicating the number of technical features indicated. Thus, features defined as "first" and "second" may explicitly or implicitly include one or more of the features. In the description of the embodiments of the present application, unless otherwise specified, "multiple" means two or more.

[0053] In order to facilitate understanding of an ultrasonic imaging method, device and apparatus provided in the embodiments of the present application, some terms in the embodiments of the present application are explained below to facilitate understanding by those skilled in the art.

[0054] (1) Frame rate (FR): The number of frames or images shown or displayed per second. Imaging frame rate refers to the number of images per second.

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

[0056] In the process of 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 is a schematic diagram of a traditional blood flow imaging timing in the related art, such as Figure 1 As shown, B1, B2... are the background (grayscale) image timing, marked with dotted line frames, that is, B1, B2... correspond to one frame of background image respectively; C1, C2... are the foreground (blood flow) image timing, marked with solid line frames, that is, C1, C2... correspond to one frame of foreground image respectively.

[0057] Each background image is collected using N scanning lines, that is, each frame of the foreground image corresponds to N scanning line areas. When collecting each frame of the image, N focused beams need to be emitted. Each focused beam corresponds to a different scanning line area. The acquisition sequence is {b1, b2, …, b N} represents, where each b corresponds to a focused beam.

[0058] Each foreground image is collected using M scanning lines, that is, each frame of foreground image corresponds to M scanning line areas, and each scanning line is emitted E1 times of focusing beams (that is, the frame packet length is E1). That is, when collecting each frame of image, M×E1 focusing beams need to be emitted, and each adjacent M focusing beams correspond to different scanning line areas. The acquisition timing is {c1, c2, …, c M×E1} represents, where each c corresponds to a focused beam.

[0059] The overall image timing is in the order of B1, C1, B2, C2, ... and so on.

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

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

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

[0063] Ultrasonic plane wave imaging is a new imaging technology that increases data acquisition efficiency by several to dozens of times compared to traditional focused beams, and can greatly improve the speed sensitivity and spatial resolution of blood flow imaging. However, since plane wave imaging does not have the ability to focus the emission, its performance on ultrasonic grayscale images is poorer than that of traditional focused beams. Therefore, to ensure image quality, when implementing 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. When designing the acquisition timing of the plane beam, if the acquisition timing of the focused beam is used, the corresponding blood flow imaging timing is as follows: Figure 2 shown.

[0064] like Figure 2 As shown in Figure 1, the background image is still acquired by line scanning using a focused beam, while the foreground image is acquired by frame scanning using a plane beam. Figure 1 Same, see Figure 1Corresponding description. The foreground image sequence is still C1, C2..., marked with a solid line frame, that is, C1, C2... corresponds to a frame of foreground image. For each frame of foreground image, plane wave acquisition with A emission angles is used, and each angle is transmitted E2 times (that is, the frame packet length is E2). That is, when collecting each frame of image, A×E2 plane wave beams need to be emitted, and each adjacent A plane beams correspond to different emission angles. The acquisition sequence is {c1, c2, ..., c A×E2} indicates that the overall image timing and Figure 1 same.

[0065] At this time, 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, that is, M×E1≈A×E2, E2 is much larger than E1, which means that the performance of plane wave blood flow imaging is generally much greater than that of traditional blood flow imaging.

[0068] However, since the background image has a fixed acquisition time, there is a trade-off between the overall imaging frame rate and the frame packet length. Therefore, for plane wave imaging, it is generally hoped that the frame packet length is greater than 64 to obtain a better imaging effect. Figure 2 As shown in the image timing, the acquisition time of the focused beam will limit the acquisition time of the planar beam, and the final imaging frame rate is generally lower than 20 Hz (Hertz), which is difficult to meet actual clinical needs.

[0069] Based on this, the embodiments of the present application provide an ultrasonic diagnostic instrument, an ultrasonic imaging method, a device and a medium, which are applied to ultrasonic examination of the human body. The two emission modes of plane beam and focused beam are combined to rearrange the acquisition sequences of the foreground image and the background image respectively, so as to solve the time-occupancy problem of the focused beam, so that the foreground imaging frame rate is not limited by the frame packet length, and the imaging frame rate of plane wave blood flow imaging is improved.

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

[0071] The following describes an optional application scenario of an ultrasonic imaging method provided by an embodiment of the present application in conjunction with the accompanying drawings. Figure 3 The ultrasonic diagnostic instrument 30 shown includes a probe 301 and a processor 302, wherein:

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

[0073] The processor 302 is used to generate, for the n+1th frame of ultrasonic image, a background image corresponding to the above-mentioned n+1th frame of ultrasonic image based on the acquisition data of N focused beams corresponding to the n+1th frame, and the above-mentioned N focused beams are adjacent focused beams; and generate a foreground image corresponding to the above-mentioned n+1th frame of ultrasonic image based on the acquisition data of M plane beams corresponding to the n+1th frame, and the above-mentioned M plane beams are adjacent plane beams, and the first MN plane beams among the M plane beams corresponding to the above-mentioned n+1th frame are the last MN plane beams among the M plane beams corresponding to the nth frame; wherein n, M and N are positive integers; based on the background image and foreground image corresponding to each frame of ultrasonic image, respectively, synthesize the ultrasonic image of the corresponding frame.

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

[0075] In addition, the present application embodiment also provides an optional application scenario of the ultrasonic 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] The ultrasound device 40 is used to respond to an ultrasound image generation instruction for a target area. The probe 402 is placed in the target area of ​​the human body. The probe 402 alternately transmits a first beam set and a second beam set, and receives acquisition data corresponding to each focused beam and a plane beam, and sends the received acquisition data to the server 41; the first beam set includes at least one focused beam, and the second beam set includes at least one plane beam; and each frame of ultrasound image sent by the server 41 is received, and displayed in the corresponding display area through the display screen 401.

[0078] The server 41 is used to generate, for the n+1th frame of ultrasonic image, a background image corresponding to the above-mentioned n+1th frame of ultrasonic image based on the acquisition data of N focused beams corresponding to the n+1th frame, and the above-mentioned N focused beams are adjacent focused beams; and to generate a foreground image corresponding to the above-mentioned n+1th frame of ultrasonic image based on the acquisition data of M plane beams corresponding to the n+1th frame, and the above-mentioned M plane beams are adjacent plane beams, and the first MN plane beams among the M plane beams corresponding to the above-mentioned n+1th frame are the last MN plane beams among the M plane beams corresponding to the nth frame; wherein n, M and N are positive integers; based on the background image and foreground image corresponding to each frame of ultrasonic image, respectively, synthesize the ultrasonic image of the corresponding frame; and send each frame of ultrasonic image to the ultrasonic device 40.

[0079] Of course, the method provided in the embodiment of the present application is not limited to Figure 3 or Figure 4 The application scenario shown can also be used in other possible application scenarios, which are not limited in the embodiments of the present application.

[0080] like Figure 5 As shown, a flow chart of an ultrasonic imaging method according to an embodiment of the present application is shown, and the specific steps are as follows:

[0081] Step S501 : in response to an instruction for generating an ultrasound image of a target area, alternately transmitting a first beam set and a second beam set.

[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 area is a body area of ​​a target object selected manually, such as a thyroid area, a heart area, etc. When there is a need to generate an ultrasound image of the target area, an ultrasound image generation instruction may be sent to a device for performing ultrasound imaging. In the embodiments of the present application, there is no limitation on the sending method of the above instruction, for example, the instruction may be sent by inputting a specific sentence or clicking a specific area.

[0084] After receiving the ultrasound image generation instruction, the first beam set and the second beam set are transmitted alternately, and the acquisition data corresponding to each transmitted beam (i.e., feedback data from the target area) is received, so as to select part of the data from the received acquisition data for image generation.

[0085] It should be noted that in the embodiment of the present application, there is no restriction on the number of beams included in the combination of the first beam set and the second beam, and different numbers can be selected based on needs in the specific implementation. At the same time, in the embodiment of the present application, the number of beams included in the first or second beam set of adjacent multiple transmissions can be completely the same, have the same periodicity, or be different.

[0086] Step S502: for the n+1th frame of ultrasound image, based on the acquisition data of the N focused beams corresponding to the n+1th frame, a background image corresponding to the n+1th frame of ultrasound image is generated; and based on the acquisition data of the Et plane beams corresponding to the n+1th frame, a foreground image corresponding to the n+1th frame of ultrasound image is generated, and the first Et-N plane beams among the Et plane beams corresponding to the n+1th frame are the last Et-N plane beams among the Et plane beams corresponding to the nth frame. n, N and Et are positive integers.

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

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

[0089] In the embodiments of the present application, the values ​​of N, A and E2 are not limited and can be set based on demand. In some embodiments, in order to optimize the imaging effect, the value of A is usually set as large as possible to improve the imaging effect if the performance of the ultrasound imaging system (data transmission efficiency, firmware and host computer memory, system computing efficiency, etc.) can support 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 areas 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 N adjacent focused beams; each adjacent A plane beams correspond to different emission angles, and the foreground image corresponding to each frame of ultrasound image is generated based on the acquisition data corresponding to the adjacent Et plane beams, where Et=A×E2.

[0091] In the embodiment of the present application, in order to ensure the subsequent beam synthesis calculation (generating the foreground image of the corresponding frame based on Et plane beams), it is necessary to ensure that the number of scanning lines N and the number of emission angles A of the foreground plane beam are integer multiples, that is, N is an integer multiple of A. In some embodiments, the above-mentioned beam synthesis calculation can be implemented by plane wave coherent compounding technology. Since the above-mentioned process of generating a background image based on the acquisition data of N focused beams and generating a foreground image based on the acquisition data of Et plane beams is a prior art, it will not be elaborated 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 plane beams corresponding to the first frame.

[0093] Step S503 : synthesizing the ultrasonic image of the corresponding frame based on the background image and the foreground image respectively corresponding to each frame of the ultrasonic image.

[0094] The above method uses plane waves and focused beams at the same time, taking into account the foreground and background quality of ultrasound imaging; and rearranges the acquisition sequence of 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 the above steps S501-S503 of the embodiment of the present application is set for the general scenario where Et is much greater than N, that is, the minimum value of E2 is N / A. When the difference between the values ​​of Et and N is small, the values ​​of Et and N are equal, or Et is less than N, the relationship between Et and N can be appropriately increased by increasing E2, or by reducing N through multi-beam reception (Multi-Line Acquisition, MLA for short) technology, so that Et is much greater than N. In a specific implementation, the above-mentioned degree of being much greater than the corresponding degree can be set manually, for example, when Et is greater than ten times of N, it is set that Et is much greater than N, or when Et is greater than one hundred times of N, it is set that 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. B =PRF C ) calculated, for parts with shallow imaging depth such as thyroid and breast, N=140 and A=7 can be set, and the theoretical imaging frame rate at an imaging depth of 4 cm is about 68.7 Hz; for abdominal parts such as liver and kidney, N=140 and A=5 can be set, and the theoretical imaging frame rate at an imaging depth of 10 cm is about 27.5 Hz; for the heart, N=90 and A=3 or 5 can be set, and the theoretical imaging frame rate at an imaging depth of 15 cm is about 28.5 Hz.

[0097] The following combination Figure 6-11 , the above-mentioned ultrasonic imaging method is 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 plane beam, then in the above step S502: the N focused beams corresponding to the n+1th frame are: the focused beams included in the N×n+1th to N×(n+1)th first beam sets; the Et plane beams corresponding to the n+1th frame are: the plane beams included in the N×n+1th to N×n+Etth second beam sets.

[0099] Figure 6 A collection combination of each pair of background and foreground images is shown. Figure 6 In the figure, B1, B2... are the background image sequence, marked with dotted line frames, that is, B1, B2... correspond to one frame of background image respectively; C1, C2... are the foreground image sequence, marked with solid line frames, that is, C1, C2... correspond to one frame of foreground image respectively.

[0100] like Figure 6 As shown, N is the total number of focused beams (each focused beam corresponds to a scanning line area) required for each frame of background image. Each frame of background image corresponds to N focused beams, that is, B1, B2, ... correspond to N focused beams (represented by b in the figure). Since each first beam set includes a focused beam, one b is equivalent to a first beam set. At this time, the N focused beams corresponding to the n+1th frame are: the focused beams included in the N×n+1th 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 is the total number of plane beams required for each frame of foreground image. Each frame of foreground image corresponds to Et plane beams, that is, C1, C2, ... correspond to Et plane beams (represented by c in the figure). Since each second beam set includes a plane beam, one c is equivalent to a second beam set. At this time, the Et plane beams corresponding to the n+1th frame are: the plane beams included in the N×n+1th to N×n+Etth 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 acquisition timing of the image is in the order of b1, c1, b2, c2, ..., and so on.

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

[0104] FR3=(N×(PRF B +PRF C )) -1 .

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

[0106] and Figure 1 and Figure 2 Compared with the related art shown, Figure 6 The emission timing of the focused beam and the plane beam shown in the figure has an overall imaging frame rate that is only determined by the frame rate of the background image and is not affected by the frame packet length E2 of the plane beam and the number of emission angles A of the plane beam. This solves the compromise problem between the frame packet length and the 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 larger than N, such as ultrasound super-resolution (Super-resolution) imaging or ultrasound localization microscopy (ULM) imaging technology, Et is generally thousands to tens of thousands. In this case, each first beam set can be set to include a focused beam, and each second beam set can include A plane beams. Then in the above step S502: the N focused beams corresponding to the n+1th frame are: the focused beams included in the N×n+1th to N×(n+1)th first beam sets; the Et plane beams corresponding to the n+1th frame are: the plane beams included in the N×n+1th to N×n+Et / Ath second beam sets.

[0108] Figure 7 A collection combination of each pair of background and foreground images is shown. Figure 7 In the figure, B1, B2... are the background image sequence, marked with dotted line frames, that is, B1, B2... correspond to one frame of background image respectively; C1, C2... are the foreground image sequence, marked with solid line frames, that is, C1, C2... correspond to one frame of foreground image respectively.

[0109] like Figure 7As shown, N is the total number of focused beams (each focused beam corresponds to a scanning line area) required for each frame of background image. Each frame of background image corresponds to N focused beams, that is, B1, B2, ... correspond to N focused beams (represented by b in the figure). Since each first beam set includes a focused beam, one b is equivalent to a first beam set. At this time, the N focused beams corresponding to the n+1th frame are: the focused beams included in the N×n+1th 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 is the total number of plane beams required for each frame of foreground image. Each frame of foreground image corresponds to Et plane beams, that is, C1, C2, ... correspond to Et plane beams (represented by c in the figure). Since each second beam set includes A plane beams, A c is equivalent to a second beam set. At this time, the Et plane beams corresponding to the n+1th frame are: the plane beams included in the N×n+1th to N×n+Et / Ath second beam sets, that is, each frame corresponds to Et / A (i.e. E2) second beam sets. For example, C1 corresponds to {c1, c2, ..., c Et}, including the 1st to E2nd second beam sets; C2 corresponds to {c A×N+1 ,c A×N+2 ,…,c A×N+Et}, which includes the N+1th to N+E2th second beam sets.

[0111] The overall image acquisition sequence is b1, {c1, c2, …, c A}, b2, {c A+1 ,c A+2 ,…,c 2A}, b3…, and so on.

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

[0113] Figure 8A collection combination of each pair of background and foreground images is shown. Figure 8 In the figure, B1, B2... are the background image sequence, marked with dotted line frames, that is, B1, B2... correspond to one frame of background image respectively; C1, C2... are the foreground image sequence, marked with solid line frames, that is, C1, C2... correspond to one frame of foreground image respectively.

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

[0115] Et is the total number of plane beams required for each frame of foreground image. Each frame of foreground image corresponds to Et plane beams, that is, C1, C2, ... correspond to Et plane beams (represented by c in the figure). Since each second beam set includes a plane beam, one c is equivalent to a second beam set. At this time, the Et plane beams corresponding to the n+1th frame are: the plane beams included in the n×N / k+1th to n×N / k+Etth second beam sets; 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 {b1, b2, …, b k}、c1、{b k+1 ,b k+2 ,…,b 2k}, c2…, and so on.

[0117] In some embodiments, when the first beam set and the second beam set are transmitted alternately, after transmitting any of the second beam sets, a preset idle time corresponding to the second beam set is separated and the first beam set is transmitted. The preset idle time is the idle time p.

[0118] It should be noted that the preset idle time durations corresponding to each second beam set may be the same or different.

[0119] Fig. 9 It represents a collection combination of each pair of background and foreground images, B1 from b1 to b N Composition, B2 consists of b N+1 To b 2N Composition, and so on; C1 consists of c1 to c Et Composition, C2 is composed of c N+1 to c N+Et Composition, and so on.

[0120] Fig. 9 Based on Figure 6 A variation of , which can be used to adjust the PRF C In the scenario, add an idle time p1, p2... after the acquisition sequence c1, c2..., marked with a diagonal box. By uniformly adjusting different idle times, the PRF can be changed. C To measure blood flow velocity at different scales. The overall acquisition sequence is in 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 time p1, p2, etc. may not be a fixed value. For example, {p1 = p3 = p5 = ... = p odd , p2=p4=p6=…p even}, where odd and even represent odd and even numbers respectively, that is, two PRFs are set in the same imaging sequence C , which is used to solve the velocity ambiguity problem in blood flow imaging. Similarly, multiple PRFs can be set in the same imaging sequence. C , to meet various measurement needs.

[0122] Fig.10 It represents a collection combination of each pair of background and foreground images, B1 from b1 to b N Composition, B2 consists of b N+1 To b 2N Composition, and so on; C1 consists of c1 to c Et Composition, C2 is composed of c A×N+1 to c A×N+Et Composition, and so on.

[0123] Fig.10 Based on Figure 7A variation of can be used in scenarios where Et is much larger than N, such as ultrasound super-resolution or ultrasound localization microscopy (ULM) imaging technology, where Et is generally 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 idle time p1, p2, etc. can be adjusted arbitrarily, and multiple PRFs can be set in the same imaging sequence. C .

[0124] Fig.11 It represents a collection combination of each pair of background and foreground images, B1 from b1 to b N Composition, B2 consists of b N+1 To b 2N Composition, and so on; C1 consists of c1 to c Et Composition, C2 is composed of c N / k+1 to c N / k+Et Composition, and so on.

[0125] Fig.11 Based on Figure 8 A variation of the overall acquisition sequence is {b1,b2,…,b k}, c1, p1, {b k+1 ,b k+2 ,…,b 2k The idle time p1, p2, etc. can be adjusted arbitrarily, and multiple PRFs can be set in the same imaging sequence. C . Under the premise that N and A are integer multiples and N is an integer multiple of k, k can also be adjusted arbitrarily.

[0126] Based on the same inventive concept, Fig.12 As shown, the embodiment of the present application provides an ultrasonic imaging device 1200, which can be specifically applied to the ultrasonic diagnostic instrument in the above embodiment, including:

[0127] The transmitting module 1201 is configured to alternately transmit a first beam set and a second beam set in response to an instruction for generating an ultrasound image of 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 generating module 1202 is used for generating, for the n+1th frame of ultrasound image, a background image corresponding to the n+1th frame of ultrasound image based on the acquisition data of N focused beams corresponding to the n+1th frame, wherein the N focused beams are adjacent focused beams; and generating, based on the acquisition data of Et plane beams corresponding to the n+1th frame of ultrasound image, a foreground image corresponding to the n+1th frame of ultrasound image, wherein the Et plane beams are adjacent plane beams, and the first Et-N plane beams among the Et plane beams corresponding to the n+1th frame are the last Et-N plane beams among the Et plane beams corresponding to the nth frame; wherein n, Et and N are positive integers; wherein n, Et and N are positive integers;

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

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

[0131] Each of the A adjacent plane beams corresponds to a different emission angle;

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

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

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

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

[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+1th frame are: the focused beams included in the N×n+1th to N×(n+1)th first beam sets;

[0138] The Et plane beams corresponding to the n+1th frame are the plane beams included in the N×n+1th to N×n+Et / Ath second beam sets.

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

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

[0141] The Et plane beams corresponding to the (n+1)th frame are the plane beams included in the (N×n / k+1)th to (N×n / k+Et)th second beam sets.

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

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

[0144] Optionally, the generating module 1202 is further used to:

[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 plane beams corresponding to the first frame.

[0146] It should be noted that the division of modules in the embodiments of the present application is schematic and is only a logical function division. There may be other division methods in actual implementation. In addition, each functional module in each embodiment of the present application may be integrated into a processing module, or each module may exist physically separately, or two or more modules may be integrated into one module. The above-mentioned integrated modules may be implemented in the form of hardware or in the form of software functional modules.

[0147] If the integrated module is implemented in the form of a software function 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 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.

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

[0149] Based on the same inventive concept, the present application embodiment provides an electronic device, which can realize the ultrasonic imaging function discussed above, please refer to Fig.13The device includes at least one processor 1301, a memory 1302 connected to the at least one processor, and a probe 1303. The specific connection medium between the processor 1301 and the memory 1302 is not limited in the embodiment of the present application. Fig.13 The processor 1301 and the memory 1302 may be connected via a bus. The bus may be divided into an address bus, a data bus, a control bus, etc. For ease of representation, Fig.13 The fact that only one line is used in the diagram does not mean that there is only one bus or only one type of bus.

[0150] Among them, the processor 1301 is the control center of the electronic device, which can use various interfaces and lines to connect various parts of the electronic device, and realize data processing by running or executing instructions stored in the memory 1302 and calling data stored in the memory 1302. Optionally, the processor 1301 may include one or more processing units, and the processor 1301 may integrate an application processor and a modem processor, wherein the application processor mainly processes the operating system, user interface, and application programs, and the modem processor mainly processes the issuance of instructions. It is understandable that the above-mentioned 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, and in some embodiments, they may also be implemented separately on independent chips.

[0151] Processor 1301 can be a general-purpose processor, such as a central processing unit (CPU), a digital signal processor, an application-specific integrated circuit (ASIC), a field programmable gate array or other programmable logic device, a discrete gate or transistor logic device, a discrete hardware component, and can implement or execute the various methods, steps and logic block diagrams disclosed in the embodiments of the present application. A general-purpose processor can be a microprocessor or any conventional processor, etc. The steps of the method disclosed in the embodiment of the test data generation method can be directly embodied as a hardware processor for execution, or a combination of hardware and software modules in the processor for execution.

[0152] Memory 1302 is a non-volatile computer-readable storage medium that 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 (Random Access Memory, RAM), static random access memory (Static Random Access Memory, SRAM), programmable read-only memory (Programmable Read Only Memory, PROM), read-only memory (Read Only Memory, ROM), electrically erasable programmable read-only memory (Electrically Erasable Programmable Read-Only Memory, EEPROM), magnetic memory, disk, optical disk, etc. Memory 1302 is any other medium that can be used to carry or store a desired program code in the form of an instruction or data structure and can be accessed by a computer, but is not limited thereto. The memory 1302 in the embodiment of the present application can also be a circuit or any other device that can realize a storage function, for storing program instructions and / or data.

[0153] In the embodiment of the present application, the memory 1302 stores a computer program, and when the program is executed by the processor 1301, the above-mentioned ultrasound imaging method is implemented.

[0154] Those skilled in the art will appreciate that the embodiments of the present application may be provided as methods, systems, or computer program products. Therefore, the present application may adopt the form of a complete hardware embodiment, a complete software embodiment, or an embodiment in combination with software and hardware. Moreover, the present application may adopt the form of a computer program product implemented in one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) that include computer-usable program code.

[0155] The present application is described with reference to the flowcharts and / or block diagrams of the methods, devices (systems), and computer program products according to the present application. It should be understood that each process and / or box in the flowchart and / or block diagram, as well as the combination of the processes and / or boxes in the flowchart and / or block diagram, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing device to produce a machine, so that the instructions executed by the processor of the computer or other programmable data processing device generate instructions for implementing the processes in the flowchart and / or block diagram. Figure 1 A process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0156] These computer program instructions may also be stored in a computer-readable memory capable of directing a computer or other programmable data processing device to operate in a specific manner, so that the instructions stored in the computer-readable memory produce an article of manufacture comprising an instruction device, which implements the process Figure 1 A process or multiple processes and / or boxes Figure 1 A function specified in one or more boxes.

[0157] These computer program instructions can also be loaded onto a computer or other programmable data processing device so that a series of operating steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing instructions for implementing the process. Figure 1 A process or multiple processes and / or boxes Figure 1 The steps for the functions specified in one or more boxes.

[0158] Obviously, those skilled in the art can make various changes and modifications to the present application without departing from the spirit and scope of the present application. Thus, if these modifications and variations of the present application fall within the scope of the claims of the present application and their equivalents, the present application is also intended to include these modifications and variations.

Claims

1. An ultrasonic diagnostic instrument, characterized in that: Including a probe and a processor; The probe is used to be placed in a target area of ​​a human body, and in response to an instruction for generating an ultrasound image of the target area, alternately transmit 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 used to generate, for the n+1th frame of ultrasonic image, a background image corresponding to the n+1th frame of ultrasonic image based on the acquisition data of N focused beams corresponding to the n+1th frame, wherein the N focused beams are adjacent focused beams; and to generate a foreground image corresponding to the n+1th frame of ultrasonic image based on the acquisition data of Et plane beams corresponding to the n+1th frame, wherein the Et plane beams are adjacent plane beams, and the first Et-N plane beams among the Et plane beams corresponding to the n+1th frame are the last Et-N plane beams among the Et plane beams corresponding to the nth frame; wherein n, Et and N are positive integers; and based on the background image and foreground image corresponding to each frame of ultrasonic image, synthesize the ultrasonic image of the corresponding frame.

2. The ultrasonic diagnostic instrument according to claim 1, characterized in that: Each of the adjacent N focused beams corresponds to a different scan line area of ​​the target area; Each of the A adjacent plane beams corresponds to a different emission angle; Wherein, A is a positive integer, and Et and N are multiples of A respectively.

3. The ultrasonic diagnostic instrument according to claim 1, characterized in that: 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+1th frame are: the focused beams included in the N×n+1th to N×(n+1)th first beam sets; The Et plane beams corresponding to the (n+1)th frame are the plane beams included in the (N×n+1)th to (N×n+Et)th second beam sets.

4. The ultrasonic diagnostic instrument according to claim 2, characterized in that: If each first beam set includes a focused beam, and each second beam set includes A planar beams, then: The N focused beams corresponding to the n+1th frame are: the focused beams included in the N×n+1th to N×(n+1)th first beam sets; The Et plane beams corresponding to the n+1th frame are the plane beams included in the N×n+1th to N×n+Et / Ath second beam sets.

5. The ultrasonic diagnostic instrument according to claim 1, characterized in that: If each first beam set includes k focused beams, and each second beam set includes a plane beam, k is a positive integer, and N is a multiple of k, then: The N focused beams corresponding to the n+1th frame are: the focused beams included in the N×n / k+1th to N×(n+1) / kth first beam sets; The Et plane beams corresponding to the (n+1)th frame are the plane beams included in the (N×n / k+1)th to (N×n / k+Et)th second beam sets.

6. The ultrasonic diagnostic instrument according to any one of claims 1 to 5, characterized in that: The probe is also used for: After transmitting any of the second beam sets, the first beam set is transmitted after a preset idle time period corresponding to the any of the second beam sets.

7. The ultrasonic diagnostic instrument according to any one of claims 1 to 5, characterized in that: The processor is further configured to: For the first frame of ultrasound image, based on the acquisition data of N focused beams corresponding to the first frame, generate a background image corresponding to the first frame of ultrasound image; And based on the acquisition data of Et plane beams corresponding to the first frame, a foreground image corresponding to the first frame of ultrasound image is generated; based on the background image and foreground image corresponding to the first frame of ultrasound image, the first frame of ultrasound image is synthesized.

8. An ultrasonic imaging method, characterized in that: The method comprises: In response to an instruction for generating an ultrasound image of a target area, 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+1th frame of ultrasound image, based on the acquisition data of N focused beams corresponding to the n+1th frame, a background image corresponding to the n+1th frame of ultrasound image is generated, and the N focused beams are adjacent focused beams; and based on the acquisition data of Et plane beams corresponding to the n+1th frame, a foreground image corresponding to the n+1th frame of ultrasound image is generated, and the Et plane beams are adjacent plane beams, and the first Et-N plane beams among the Et plane beams corresponding to the n+1th frame are the last Et-N plane beams among 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 the ultrasonic image, the ultrasonic image of the corresponding frame is synthesized.

9. An ultrasonic imaging device, characterized in that: The device comprises: A transmitting module, configured to alternately transmit a first beam set and a second beam set in response to an instruction for generating an ultrasound image of 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, for generating, for an n+1th frame of ultrasonic image, a background image corresponding to the n+1th frame of ultrasonic image based on the acquisition data of N focused beams corresponding to the n+1th frame, wherein the N focused beams are adjacent focused beams; and foreground image corresponding to the n+1th frame of ultrasonic image based on the acquisition data of Et plane beams corresponding to the n+1th frame, wherein the Et plane beams are adjacent plane beams, and the first Et-N plane beams among the Et plane beams corresponding to the n+1th frame are the last Et-N plane beams among the Et plane beams corresponding to the nth frame; wherein n, Et and N are positive integers; wherein n, Et and N are positive integers; The synthesis module is used to synthesize the ultrasonic image of the corresponding frame based on the background image and the foreground image corresponding to each frame of the ultrasonic image.

10. A computer-readable storage medium having computer program instructions stored thereon, characterized in that: When the computer program instructions are executed by a processor, the steps of the method according to claim 8 are implemented.

Images