Ultrasonic image generation method and device, storage medium and program product

Abstract

The invention discloses an ultrasonic image generation method and device, a storage medium and a program product, and relates to the field of ultrasonic imaging, and the method comprises the steps: determining first target scanning data corresponding to an ith scanning line in M scanning periods based on historical scanning data obtained by a first ultrasonic probe on at least two adjacent scanning lines; the first target scanning data corresponding to the ith scanning line in M scanning periods are synthesized, synthetic data on the ith scanning line in an image generation period is obtained, and one image generation period comprises the M scanning periods; based on synthetic data of the first ultrasonic probe on the N scanning lines in one image generation period, a frame of first ultrasonic image corresponding to one image generation period is generated, the first ultrasonic image is a 360-degree annular gray level image, and M and N are positive integers. Based on the scheme provided by the embodiment of the invention, the resolution of the ultrasonic image can be effectively improved, and artifacts are inhibited.

Description

Technical Field

[0001] The present invention relates to the field of ultrasonic imaging, and in particular to an ultrasonic image generation method, device, storage medium and program product. Background Art

[0002] Nowadays, ultrasound imaging technology is widely used in the field of clinical medicine. It uses ultrasound beams to scan the human body and obtain images of internal organs by receiving and processing reflected signals to determine the scope and physical properties of lesions.

[0003] In the related art, there is a motor in the ultrasound probe, which rotates to emit ultrasound beams to different angles (different scanning lines), thereby acquiring organ image data at different angles and generating an ultrasound image based on the organ image data on different scanning lines.

[0004] However, during the imaging process, artifacts may be generated due to the width and directivity of the ultrasound beam, resulting in poor quality of the synthesized ultrasound image, which increases the difficulty of making an accurate diagnosis. Summary of the invention

[0005] The object of the present invention is to provide an ultrasonic image generation method, device, storage medium and program product, so as to suppress the occurrence of artifacts in the ultrasonic imaging process and improve the quality of the generated ultrasonic image.

[0006] To achieve one of the above-mentioned purposes of the invention, an embodiment of the present application provides a method for generating an ultrasound image, the method comprising:

[0007] Determine first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles based on historical scanning data acquired by the first ultrasonic probe on at least two adjacent scanning lines;

[0008] Synthesize the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles to obtain synthesized data on the i-th scanning line in one image generation cycle, wherein one image generation cycle includes M scanning cycles;

[0009] Based on the synthetic data of the first ultrasonic probe on N scanning lines in one image generation cycle, a frame of first ultrasonic image corresponding to one image generation cycle is generated, the first ultrasonic image is a 360-degree annular grayscale image, and M and N are both positive integers.

[0010] On the other hand, the present application provides an electronic device comprising: at least one processor; and a memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor so that the at least one processor can execute the ultrasound image generation method as described in any of the above aspects.

[0011] On the other hand, the present application provides a non-transitory computer-readable storage medium storing computer instructions, wherein the computer instructions are used to enable the computer to execute the ultrasound image generation method as described in any one of the above aspects.

[0012] On the other hand, the present application provides a computer program product, including a computer program, which, when executed by a processor, implements the ultrasound image generation method as described in any of the above aspects.

[0013] Compared with the prior art, the present invention has the following beneficial effects: In the embodiment of the present application, in the process of generating an ultrasonic image based on the data of the scanning line, the first target scanning data corresponding to the i-th scanning line is determined based on the historical scanning data obtained on at least two adjacent scanning lines, and the first target scanning data scanned based on multiple scanning cycles are synthesized to obtain the image data corresponding to the i-th scanning line in an ultrasonic image, and finally a 360-degree annular grayscale image is generated according to the corresponding image data of multiple scanning lines. In this process, the scanning data on the i-th scanning line is replaced based on the weighted result of the historical scanning data on at least two adjacent scanning lines, and a frame of image is obtained by adding multiple frames of scanning data, which can effectively suppress artifacts while improving the resolution filter of the ultrasonic image and improve the quality of the ultrasonic image. BRIEF DESCRIPTION OF THE DRAWINGS

[0014] Figure 1 A flowchart of a method for generating an ultrasound image provided by an exemplary embodiment of the present application is shown;

[0015] Figure 2 A schematic diagram of an ultrasound imaging system provided by an exemplary embodiment of the present application is shown;

[0016] Figure 3 A timing diagram of ultrasound scanning performed by a first ultrasound probe and a second ultrasound probe provided by an exemplary embodiment of the present application is shown;

[0017] Figure 4 A flowchart of performing ultrasound image display provided by an exemplary embodiment of the present application is shown;

[0018] Figure 5 A flowchart of a process for obtaining synthetic data provided by an exemplary embodiment of the present application is shown;

[0019] Figure 6 A structural block diagram of an electronic device provided by an exemplary embodiment of the present application is shown. DETAILED DESCRIPTION

[0020] The present invention will be described in detail below in conjunction with the specific embodiments shown in the accompanying drawings. However, these embodiments do not limit the present invention, and any structural, methodological, or functional changes made by a person skilled in the art based on these embodiments are all within the scope of protection of the present invention.

[0021] It should be noted that the term "comprises" or any other variation thereof is intended to cover non-exclusive inclusion, so that a process, method, article or device that includes a series of elements includes not only those elements, but also includes other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In addition, the terms "first", "second", etc. are used for descriptive purposes only and cannot be understood as indicating or implying relative importance.

[0022] Nowadays, ultrasound imaging technology is an important medical diagnostic tool and is widely used in clinical diagnosis. However, artifacts often appear in ultrasound imaging. For example, the width and directivity of the sound beam may cause some artifacts. For example, when the ultrasound probe is transmitting, the reflected signals from different depths may interfere with each other and form artifacts. And when the direction of the ultrasound beam is not ideal, the edges of the ultrasound image will appear blurred or distorted.

[0023] Therefore, in order to solve the above problems, the present application proposes an ultrasound image generation method, which uses weighted historical scanning data of adjacent scanning lines to replace the data scanned by a scanning line, and synthesizes the scanning data on multiple frames of scanning lines to obtain the image data corresponding to the scanning line in a frame of image, thereby suppressing the generation of artifacts and improving the image generation quality.

[0024] Please refer to Figure 1 , which shows a flow chart of an ultrasound image generation method provided by an exemplary embodiment of the present application. The process includes the following steps:

[0025] Step 101, based on the historical scanning data acquired by the first ultrasonic probe on at least two adjacent scanning lines, determine the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles.

[0026] There is a motor in the ultrasound probe. During the ultrasound scanning process, the motor rotates 360° to send ultrasound waves on different scanning lines. Different scanning lines have the same angle difference, and N scanning lines are distributed within a 360° circle with the ultrasound probe as the center. When the motor rotates one circle, that is, the ultrasound probe obtains a piece of scanning data on each of the N scanning lines, a scanning cycle is completed.

[0027] The scanning line refers to the propagation path of the ultrasound beam emitted by the ultrasound probe in the scanned object (such as human tissue). It is the basic unit used to obtain information inside the tissue during ultrasound imaging. The ultrasound probe can be regarded as an information acquisition source, and the scanning line is the sound line emitted from this source, which detects the structure of the object by propagating inside the object. The ultrasound image is composed of the information obtained by multiple scanning lines. In a series of scanning lines, the ultrasound probe completes multiple transmissions and receptions of reflected and scattered signals, and converts them into pixels in the image based on information such as their intensity and time delay. The pixels corresponding to multiple scanning lines are combined together to form a two-dimensional ultrasound image.

[0028] In the embodiment of the present application, the scanning data acquired by the ultrasonic probe on the scanning line is information such as the intensity and time delay of the reflected and scattered signals.

[0029] Step 102, synthesizing the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles to obtain synthesized data on the i-th scanning line in one image generation cycle.

[0030] Among them, one image generation cycle includes M scanning cycles.

[0031] The first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles is synthesized to obtain the synthesized data of one image generation cycle and generate the corresponding ultrasound image, that is, one frame of ultrasound image is generated based on the scanning data obtained by the ultrasound probe in M ​​scanning frames. In this process, the motor in the ultrasound probe rotates M times.

[0032] Step 103 : generating a frame of first ultrasound image corresponding to one image generation cycle based on the synthetic data of the first ultrasound probe on N scanning lines in one image generation cycle.

[0033] The first ultrasonic image is a 360-degree annular grayscale image, and M and N are both positive integers.

[0034] In one image generation cycle, the motor rotates M times, and each time the motor rotates one time, a portion of scanning data is obtained on the corresponding N scanning lines.

[0035] After obtaining the scanning data collected by the ultrasound probe, filtering processing is performed, and based on the filtering results, ultrasonic signal processing and image processing such as envelope extraction, logarithmic compression, speckle suppression, smoothing and coordinate transformation are performed to obtain a 360° annular grayscale image.

[0036] Generally speaking, the greater the scanning line density, that is, the greater the number of scanning lines within a unit area, the higher the image resolution. Increasing the scanning line density requires more time to transmit and receive the scanning line signals, which may reduce the imaging frame rate. In the embodiment of the present application, the image resolution is not improved by increasing the scanning line density. Instead, the target scanning data within multiple scanning cycles is synthesized and an image is generated based on the synthesized data. Therefore, the purpose of improving the resolution can be achieved.

[0037] In the embodiment of the present application, in the process of generating an ultrasonic image based on the data of the scan line, the first target scan data corresponding to the i-th scan line is determined based on the historical scan data obtained on at least two adjacent scan lines, and the first target scan data scanned based on multiple scan cycles are synthesized to obtain image data corresponding to the i-th scan line in an ultrasonic image, and finally a 360-degree annular grayscale image is generated according to the corresponding image data of multiple scan lines. In this process, the scan data on the i-th scan line is replaced based on the weighted result of the historical scan data on at least two adjacent scan lines, and a frame of image is obtained by adding multiple frames of scan data, which can effectively suppress artifacts while improving the resolution filter of the ultrasonic image and improve the quality of the ultrasonic image.

[0038] Please refer to Figure 2 , which shows a schematic diagram of an ultrasound imaging system provided by an exemplary embodiment of the present application, wherein the ultrasound imaging system includes a first ultrasound probe 201, a second ultrasound probe 202 and an electronic device 203.

[0039] The sound waves emitted by the first ultrasonic probe 201 and the second ultrasonic probe 202 have different frequencies, and upon receiving ultrasonic pulse excitation, the first ultrasonic probe 201 and the second ultrasonic probe 202 simultaneously emit ultrasonic waves to perform ultrasonic scanning.

[0040] Please refer to Figure 3 , which shows a timing diagram of a first ultrasonic probe and a second ultrasonic probe performing ultrasonic scanning provided by an illustrative embodiment of the present application. When the PRT (Pulse Repetition Time) signal reaches a falling edge, the first ultrasonic probe and the second ultrasonic probe simultaneously transmit ultrasonic signals, the waveform transmitted by the first ultrasonic probe is TX1, and the waveform transmitted by the second ultrasonic probe is TX2, and the frequencies of the ultrasonic signals transmitted by the first ultrasonic probe and the second ultrasonic probe are different.

[0041] After the first ultrasonic probe and the second ultrasonic probe acquire the scan data, the scan data is synchronously transmitted to the electronic device 203, which can be a computer device or an ultrasonic diagnostic instrument. After receiving the scan data, the electronic device filters the scan data in the two channels, and different ultrasonic probes correspond to different channels. After performing envelope extraction, logarithmic compression, speckle suppression, smoothing, coordinate transformation and other ultrasonic signal processing and image processing based on the filtering results, two 360° annular grayscale images are obtained.

[0042] In a possible implementation, after receiving the scanning data sent by the second ultrasonic probe, the electronic device determines the second target scanning data corresponding to the i-th scanning line in M ​​scanning cycles based on the historical scanning data acquired by the second ultrasonic probe on at least two adjacent scanning lines, and the first ultrasonic probe and the second ultrasonic probe transmit ultrasonic waves at different frequencies. Then, the second target scanning data corresponding to the i-th scanning line in the M scanning cycles are synthesized to obtain the synthesized data on the i-th scanning line in an image generation cycle. Finally, based on the synthesized data of the second ultrasonic probe on N scanning lines in an image generation cycle, a frame of the second ultrasonic image corresponding to an image generation cycle is generated.

[0043] One of the image generation cycles includes M scanning cycles, M and N are both positive integers, and the second ultrasound image is a 360-degree annular grayscale image. In ultrasound imaging, good ultrasound image resolution requires the use of high-frequency ultrasound. When scanning, the higher the frequency of ultrasound, the worse its penetration. Therefore, in order to take into account the resolution and penetration of ultrasound scanning, the first ultrasound probe and the second ultrasound probe with different frequencies are used to scan the same organ part, so that one ultrasound probe can have a higher resolution and the other ultrasound probe has stronger penetration. Therefore, the two ultrasound images obtained synchronously can allow relevant technicians to focus on corresponding content in different images.

[0044] In a possible implementation, the first ultrasonic image and the second ultrasonic image are generated simultaneously in different processing channels, and after generating the first ultrasonic image and the second ultrasonic image, the electronic device displays the first ultrasonic image and the second ultrasonic image based on a set display mode.

[0045] The display mode may be automatically set by the electronic device, or may be switched in real time by relevant technicians, which is not limited in this embodiment.

[0046] Optionally, the display mode includes single-frame switching display, dual-frame same-screen display, and dual-frame fusion display. Single-frame switching display is to display the first ultrasound image or the second operation image on the screen. After displaying the ultrasound image generated by one channel, the ultrasound image generated by another channel can be displayed in response to the image switching operation of the technical technician. When the display mode is dual-frame same-screen display, the first ultrasound image and the second ultrasound image are displayed on the same screen, for example, the first ultrasound image is displayed on the left side of the screen, and the second ultrasound image is displayed on the right side of the screen.

[0047] When the display mode is dual-frame fusion display, the electronic device fuses the first ultrasonic image and the second ultrasonic image generated in the same image generation cycle based on the generated first ultrasonic image and the second ultrasonic image to obtain a fused image, and displays the fused image on the screen.

[0048] Optionally, the formula for image fusion is: fused image = w1×first ultrasound image+(1-w1)×second ultrasound image, wherein w1 may be set with different weight values ​​based on the depth.

[0049] Please refer to Figure 4 , which shows a flowchart for ultrasound image display provided by an exemplary embodiment of the present application. First, a dual-frequency first ultrasound probe and a second ultrasound probe are used to scan simultaneously to obtain a first ultrasound image and a second ultrasound image. Then, it is determined whether the display mode is a dual-frame same-screen display. If it is a dual-frame same-screen display, the first ultrasound image is displayed on the left side of the screen, and the second ultrasound image is displayed on the right side. If the display mode is not a dual-frame same-screen display, it is determined whether the display mode is a single-frame fusion display. If so, the fusion image is displayed on the screen. If not, it is determined whether the first ultrasound image in the first channel is currently displayed. If so, the first ultrasound image is displayed. If not, the second ultrasound image is displayed.

[0050] In the embodiment of the present application, the method of dual-frequency dual-channel simultaneous excitation and simultaneous reception is adopted, which can take into account both resolution and penetration. And by switching different display modes, different ultrasound images are displayed, which is conducive to providing the image display required by technicians in different situations and improving applicability.

[0051] Please refer to Figure 5 , which shows a flowchart of a process of obtaining synthetic data provided by an exemplary embodiment of the present application. The process includes the following steps:

[0052] Step 501, determining target adjacent scanning lines based on an angle threshold range.

[0053] The angle threshold range is centered on the angle of the i-th scanning line.

[0054] Since there are N scanning lines distributed within the 360° circumference, each scanning line has a corresponding line number and angle. For example, a scanning cycle contains 180 scanning lines, the scanning line with line number 1 corresponds to an angle of 0°, and the scanning line with line number 2 corresponds to an angle of 2°.

[0055] The angle threshold range is the angle centered on the i-th scan line. For example, the angle threshold range is ±10°. If the angle of the i-th scan line is 10°, the corresponding target adjacent scan line angle should be 0°-20°. If a scan cycle contains 180 scan lines, the corresponding target adjacent scan line line number should be 0-10.

[0056] Step 502, based on the angle of the target adjacent scanning line and the angle of the i-th scanning line, determine the weighted weights corresponding to different target adjacent scanning lines in each scanning cycle.

[0057] In the same scanning cycle, the weighted weights corresponding to adjacent scanning lines of each target are different, and in different scanning cycles, the weighted weights corresponding to adjacent scanning lines of the same target are also different.

[0058] In a possible implementation, first weights corresponding to different target adjacent scanning lines in the first scanning cycle are determined based on the angles of the target adjacent scanning lines and the angle of the i-th scanning line. Subsequently, weights corresponding to the target scanning lines in the remaining M-1 scanning cycles are determined based on the first weights.

[0059] In a scanning cycle, since the angles of some target adjacent scanning lines are greater than the angle of the i-th scanning line, and the angles of some target adjacent scanning lines are smaller than the angle of the i-th scanning line, the corresponding weighted calculation formulas for target adjacent scanning lines with different angles should also be different.

[0060] 1. For the first ultrasound probe, if the angle of the target adjacent scanning line is not less than the angle of the i-th scanning line, the weighted weight is: WF f1 (K) = cos(angle(K)-angle(I)); If the angle of the target adjacent scan line is less than the angle of the i-th scan line, the weighted weight is: WF f1 (K)=-cos(angle(K)-angle(I)).

[0061] Wherein, K is the line number of the target adjacent scanning line, I is the line number of the i-th scanning line, angle(K) is the angle of the k-th scanning line, angle(I) is the angle of the i-th scanning line, and f1 represents the frequency of the first ultrasonic probe.

[0062] From the above formula, it can be obtained that if the angle of the target adjacent scanning line is greater than or equal to the angle of the i-th scanning line, the weighted weight corresponding to the target scanning line is negatively correlated with the difference in angles, that is, the larger the angle difference is, the smaller the weighted weight corresponding to the target scanning line is. If the angle of the target adjacent scanning line is less than the angle of the i-th scanning line, the weighted weight corresponding to the target scanning line is positively correlated with the difference in angles, that is, the larger the angle difference is, the larger the weighted weight corresponding to the target scanning line is.

[0063] In a possible implementation, one image generation cycle includes three scanning cycles, that is, the scanning data corresponding to the three scanning cycles are synthesized to obtain image data in one frame of image.

[0064] Optionally, after obtaining the first weighted weights corresponding to each target adjacent scanning line in the first scanning cycle in the first ultrasonic probe, the weighted weights corresponding to each target scanning line in the remaining M-1 scanning cycles are determined based on the first weighted weights.

[0065] Optionally, the weighted weight calculation formula for calculating the second scanning cycle and the third scanning cycle is:

[0066] WF f1 a(K)=WF f1 (K)+g1,WF f1 b(K)=-WF f1 (K)-g1

[0067] Among them, WF f1 a(K) is the second weighted weight corresponding to the scanning line with line number K in the second scanning cycle in an image generation cycle, WF f1 b(K) is the third weighted weight of the scanning line with line number K in the third scanning cycle, WF f1 (K) is the first weighted weight corresponding to the scanning line with line number K in the first scanning cycle, where g1 is a hyperparameter related to the first ultrasonic probe.

[0068] The second weighting weight and the third weighting weight are determined based on the first weighting weight, and there is no need to perform calculations based on the angle difference, thus simplifying the calculation steps.

[0069] 2. For the second ultrasonic probe, the same steps are adopted to determine the first weighted weights corresponding to different target adjacent scanning lines in the first scanning cycle based on the angle of the target adjacent scanning line and the angle of the i-th scanning line.

[0070] Optionally, if the angle of the target adjacent scan line is not less than the angle of the i-th scan line, the weighted weight is: WF f2(K) = -cos(angle(K) - angle(I)); If the angle of the target adjacent scan line is less than the angle of the i-th scan line, the weighted weight is: WF f2 (K) = cos(angle(K) - angle(I)). K is the line number of the target adjacent scanning line, I is the line number of the i-th scanning line, angle(K) is the angle of the k-th scanning line, angle(I) is the angle of the i-th scanning line, and f2 represents the frequency of the second ultrasonic probe.

[0071] Then, based on the first weighted weight, the weighted weights corresponding to the target scanning lines in the remaining M-1 scanning cycles are determined.

[0072] In a possible implementation, one image generation cycle includes three scanning cycles, that is, the scanning data corresponding to the three scanning cycles are synthesized to obtain image data in one frame of image.

[0073] Optionally, the weighted weight calculation formula for calculating the second scanning cycle and the third scanning cycle is:

[0074] WF f2 a(K)=-WF f2 (K)-g1;WF f2 b(K)=-WF f2 (K)+g1.

[0075] WF f2 a(K) is the weight of the second scanning cycle, WF f2 b(K) is the weighted value in the third scanning cycle.

[0076] Step 503, based on the weighted weights corresponding to different target adjacent scanning lines in different scanning cycles, weighted sum is performed on the historical scanning data of the target adjacent scanning lines to obtain the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles.

[0077] In a possible implementation, a register is provided in the electronic device for temporarily storing the scanning data obtained by the first ultrasonic probe and the second ultrasonic probe on each scanning line.

[0078] When the ultrasonic pulse cycle is reached, the first ultrasonic probe acquires the first scanning data on the scanning line, and then updates the first scanning data to the storage unit corresponding to the scanning line. For example, in the first register corresponding to the first ultrasonic probe, the storage unit corresponding to the i-th scanning line stores the scanning data a obtained in the first scanning cycle, and the historical scanning data of the i-th scanning line is the scanning data a at this time, and in the second scanning cycle, the first ultrasonic probe acquires the scanning data b on the i-th scanning line, and updates the scanning data b to the storage unit corresponding to the i-th scanning line, and at this time, only the scanning data b is stored in the storage unit, and the scanning data b is the historical scanning data corresponding to the current i-th scanning line.

[0079] Among them, the first scanning data stored in the storage sheet corresponding to each scanning line is the historical scanning data corresponding to the scanning line.

[0080] Furthermore, since the ultrasonic probe scans sequentially according to the line number of the scanning line within a scanning cycle, it can be understood that the historical scanning data of the target adjacent scanning line with an angle smaller than the i-th scanning line is the first scanning data obtained in the current scanning cycle, and the historical scanning data of the target adjacent scanning line with an angle greater than the i-th scanning line is the first scanning data obtained in the previous scanning cycle.

[0081] Optionally, before performing weighted summation on the historical scan data of the target adjacent scan lines, the electronic device reads the historical scan data of the target adjacent scan lines from the storage unit corresponding to the target adjacent scan lines.

[0082] 1. For the first ultrasonic probe, since the weighted weights in different scanning cycles are different, the first target scanning data corresponding to each scanning cycle is also different.

[0083] Optionally, in the first scanning cycle, the weighted summation formula for calculating the first target scanning data is:

[0084] Dataout f1 (I) = ∑ J Datain(K)*WF f1 (K)

[0085] Among them, Dataout f1 (I) is the first target scanning data corresponding to the i-th scanning line in the first scanning cycle, Datain(K) is the historical scanning data corresponding to the scanning line with line number K, WF f1 (K) is the weighted weight corresponding to the scanning line with line number K in the first scanning cycle, and J is the number of target scanning lines.

[0086] In the remaining M-1 scanning cycles, the formula for the first target scanning data of the i-th scanning line is:

[0087] Dataout f1 A(I)=∑ J Datain(K)*WF f1 a(K)

[0088] Dataout f1 B(I)=∑ J Datain(K)*WF f1 b(K)

[0089] Among them, Dataout f1 A(I) is the first target scanning data corresponding to the i-th scanning line in the second scanning cycle, Dataout f1 B(I) is the first target scanning data corresponding to the i-th scanning line in the second scanning cycle, Datain(K) is the historical scanning data corresponding to the scanning line with line number K, and J is the number of target scanning lines.

[0090] 2. For the second ultrasound probe

[0091] Optionally, in the first scanning cycle, the weighted summation formula for calculating the second target scanning data is:

[0092] Dataout f2 (I) = ∑ J Datain(K)*WF f2 (K)

[0093] Among them, Dataout f2 (I) is the second target scanning data corresponding to the i-th scanning line in the first scanning cycle, Datain(K) is the historical scanning data corresponding to the scanning line with line number K, WF f2 (K) is the weighted weight corresponding to the scanning line with line number K in the first scanning cycle, and J is the number of target scanning lines.

[0094] In the remaining M-1 scanning cycles, the formula for the second target scanning data of the i-th scanning line is:

[0095] Dataout f2 A(I)=∑ J Datain(K)*WF f2 a(K)

[0096] Dataout f2 B(I)=∑ J Datain(K)*WF f2 b(K)

[0097] Among them, Dataout f2A(I) is the second target scanning data corresponding to the i-th scanning line in the second scanning cycle, Dataout f2 B(I) is the second target scanning data corresponding to the i-th scanning line in the second scanning cycle, Datain(K) is the historical scanning data corresponding to the scanning line with line number K, and J is the number of target scanning lines.

[0098] Step 504 , synthesizing the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles to obtain synthesized data on the i-th scanning line in one image generation cycle.

[0099] Optionally, when M is 3, that is, the first scanning data corresponding to the i-th scanning line in three scanning cycles is synthesized, and the synthesized data of the first ultrasonic probe on the i-th scanning line in one image generation cycle is obtained as follows:

[0100] Dataout f1 new(I)=-Dataout f1 (I)+(Dataout f1 A(I)+Dataout f1 B(I))*0.5

[0101] Optionally, when M is 3, the second scanning data corresponding to the i-th scanning line in three scanning cycles is synthesized, and the synthesized data of the second ultrasound probe on the i-th scanning line in one image generation cycle is obtained as follows:

[0102] Dataout f2 new(I)=-Dataout f2 (I)+(Dataout f2 A(I)+Dataout f2 B(I))*0.5

[0103] Among them, Dataout f1 new(I) is the synthetic data of the first ultrasound probe on the i-th scanning line in an image generation cycle, Dataout f2 new(I) is the synthetic data of the second ultrasound probe on the i-th scanning line in an image generation cycle.

[0104] In a possible implementation, the directivity of the scanning data acquired by an ultrasound probe before weighted synthesis is approximately:

[0105]

[0106] Among them, p is the width of the ultrasonic probe, w is the number of sound waves, and theta is the azimuth angle of the sound beam.

[0107] After synthesis based on the solution provided in the embodiment of the present application, the directionality of the target scanning data obtained is:

[0108]

[0109] Among them, N is the number of adjacent scanning lines of the target. After comparing the above two formulas, it can be seen that the main lobe width of the sound beam of Vnew is narrower than V, and the side lobe is suppressed. Therefore, the solution provided in this application can effectively improve the resolution and suppress artifacts.

[0110] In an embodiment of the present application, the target scanning data obtained by weighted merging of historical scanning data on multiple adjacent scanning lines replaces the scanning data scanned on the i-th scanning line, and the historical scanning data obtained in multiple scanning cycles are weighted and merged to obtain synthetic data, thereby generating an ultrasound image, which is beneficial to improving resolution and reducing artifacts.

[0111] Please refer to Figure 6 , which shows a structural block diagram of an electronic device provided by an exemplary embodiment of the present application. The electronic device in the present application may include one or more of the following components: a processor 610 and a memory 620.

[0112] Optionally, the processor 610 executes the steps of the ultrasound image generation method provided in any of the above embodiments by running or executing instructions, programs, code sets or instruction sets stored in the memory 1520, and calling data stored in the memory 620.

[0113] In addition, the processor can also perform various functions of the device and process data. Optionally, the processor 610 can be implemented in at least one hardware form of digital signal processing (DSP), field-programmable gate array (FPGA), and programmable logic array (PLA). The processor 610 can integrate one or a combination of a central processing unit (CPU), a graphics processing unit (GPU), a neural network processor (NPU), and a modem. Among them, the CPU mainly processes the operating system, user interface, and application programs; the GPU is responsible for rendering and drawing the content to be displayed on the touch display; the NPU is used to implement artificial intelligence (AI) functions; and the modem is used to process wireless communications. It can be understood that the above-mentioned modem may not be integrated into the processor 1510, but may be implemented separately through a chip.

[0114] The memory 620 may include a random access memory (RAM) or a read-only memory (ROM). Optionally, the memory 620 includes a non-transitory computer-readable storage medium. The memory 620 may be used to store instructions, programs, codes, code sets, or instruction sets. The memory 620 may include a program storage area and a data storage area, wherein the program storage area may store instructions for implementing an operating system, instructions for at least one function (such as a touch function, a sound playback function, an image playback function, etc.), instructions for implementing the following various method embodiments, etc.; the data storage area may store data created according to the use of the device (such as audio data, a phone book), etc.

[0115] The device in the embodiment of the present application further includes a communication component 630 and a display component 640. The communication component 630 may be a Bluetooth component, a WiFi (WIREless-Fidelity) component, an NFC (Near Field Communication) component, etc., for communicating with an external device (server or other device) via a wired or wireless network; the display component 640 is used to display a graphical user interface and / or receive user interaction operations.

[0116] In addition, those skilled in the art will appreciate that the structure of the device shown in the above drawings does not constitute a limitation on the device, and the device may include more or fewer components than shown, or combine certain components, or arrange the components differently. For example, the device also includes components such as a radio frequency circuit, an input unit, a sensor, an audio circuit, a speaker, and a power supply, which will not be described in detail here.

[0117] An embodiment of the present application also provides a non-transitory computer-readable storage medium storing computer instructions, wherein the storage medium stores at least one program code, and the program code is loaded and executed by a processor to implement the ultrasound image generation method described in any of the above embodiments.

[0118] The embodiment of the present application provides a computer program product, which includes computer instructions stored in a computer-readable storage medium. When the computer program is executed by a processor, the method for generating an ultrasound image as described in any of the above embodiments is implemented.

Claims

1. A method for generating an ultrasonic image, characterized in that: The method comprises: Determine first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles based on historical scanning data acquired by the first ultrasonic probe on at least two adjacent scanning lines; Synthesize the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles to obtain synthesized data on the i-th scanning line in one image generation cycle, wherein one image generation cycle includes M scanning cycles; Based on the synthetic data of the first ultrasonic probe on N scanning lines in one image generation cycle, a frame of first ultrasonic image corresponding to one image generation cycle is generated, the first ultrasonic image is a 360-degree annular grayscale image, and M and N are both positive integers.

2. The method according to claim 1, characterized in that The determining, based on the historical scanning data acquired by the first ultrasonic probe on at least two adjacent scanning lines, first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles includes: Determining target adjacent scanning lines based on an angle threshold range, wherein the angle threshold range is centered on the angle of the i-th scanning line; Based on the angle of the target adjacent scanning line and the angle of the i-th scanning line, determining the weighted weights corresponding to the adjacent scanning lines of different targets in each scanning cycle; Based on the weighted weights corresponding to adjacent scanning lines of different targets in different scanning cycles, the historical scanning data of the adjacent scanning lines of the targets are weightedly summed to obtain the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles.

3. The method according to claim 2, characterized in that The method further comprises: When the ultrasonic pulse cycle is reached, controlling the first ultrasonic probe to acquire first scanning data on the scanning line; The first scanning data is updated to the storage unit corresponding to the scanning line, and the first scanning data stored in the storage unit corresponding to each scanning line is the historical scanning data corresponding to the scanning line; The historical scanning data of the target adjacent scanning line with an angle smaller than the i-th scanning line is the first scanning data acquired in the current scanning cycle, and the historical scanning data of the target adjacent scanning line with an angle larger than the i-th scanning line is the first scanning data acquired in the previous scanning cycle; Before performing weighted summation on the historical scan data of the target adjacent scan lines, the method further includes: The historical scan count of the target adjacent scan line is read from a storage unit corresponding to the target adjacent scan line.

4. The method according to claim 2, characterized in that: The determining, based on the angle of the target adjacent scanning line and the angle of the i-th scanning line, the weighted weights corresponding to the adjacent scanning lines of different targets in each scanning cycle includes: Determine first weights corresponding to different target adjacent scanning lines in the first scanning cycle based on the angle of the target adjacent scanning line and the angle of the i-th scanning line; Based on the first weighted weight, the weighted weight corresponding to each of the target scanning lines in the remaining M-1 scanning cycles is determined.

5. The method according to claim 4, characterized in that The determining, based on the angle of the target adjacent scanning line and the angle of the i-th scanning line, first weighted weights corresponding to different target adjacent scanning lines in the first scanning cycle respectively includes: If the angle of the target adjacent scanning line is not less than the angle of the i-th scanning line, the weighted weight is: WF f1 (K)=cos(angle(K)-angle(I)); If the angle of the target adjacent scan line is less than the angle of the i-th scan line, the weighted weight is: WF f1 (K)=-cos(angle(K)-angle(I)); Wherein, K is the line number of the target adjacent scanning line, I is the line number of the i-th scanning line, angle(K) is the angle of the k-th scanning line, angle(I) is the angle of the i-th scanning line, and f1 represents the frequency of the first ultrasonic probe.

6. The method according to claim 4, characterized in that In the step of "performing a weighted summation of the historical scan data of the target adjacent scan lines", the weighted summation formula corresponding to the first scan cycle is: Dataout f1 (I)=∑ J Datain(K)*WF f1 (K), Among them, Dataout f1 (I) is the first target scanning data corresponding to the i-th scanning line in the first scanning cycle, Datain(K) is the historical scanning data corresponding to the scanning line with line number K, and WF f1 (K) is the weighted weight corresponding to the scanning line with line number K in the first scanning cycle, and J is the number of the target scanning lines.

7. The method according to claim 4, characterized in that One image generation cycle includes three scanning cycles; In the step of "determining the weighted weights corresponding to the target scan lines in the remaining M-1 scan cycles based on the first weighted weights", the calculation formula for the weighted weights of the target scan lines in the remaining M-1 scan cycles is: WF f1 a(K)=WF f1 (K)+g1 WF f1 b(K)=-WF f1 (K)-g1 Among them, WF f1 a(K) is the second weighted weight corresponding to the scanning line with line number K in the second scanning cycle in an image generation cycle, WF f1 b(K) is the third weighted weight of the scanning line with line number K in the third scanning cycle, WF f1 (K) is the first weighted weight corresponding to the scanning line with line number K in the first scanning cycle, where g1 is a hyperparameter related to the first ultrasonic probe.

8. The method according to claim 1, characterized in that: In the step of "performing a weighted summation of the historical scan data of the target adjacent scan lines", the formula for determining the first target scan data of the i-th scan line in the remaining M-1 scan cycles is: Dataout f1 A(I)=∑ J Datain(K)*WF f1 a(K) Dataout f1 B(I)=∑ J Datain(K)*WF f1 b(K) Among them, Dataout f1 A(I) is the first target scanning data corresponding to the i-th scanning line in the second scanning cycle, Dataout f1 B(I) is the first target scanning data corresponding to the i-th scanning line in the second scanning cycle, Datain(K) is the historical scanning data corresponding to the scanning line with line number K, and J is the number of the target scanning lines.

9. The method according to claim 7, characterized in that: In the step of "synthesizing the first target scanning data corresponding to the i-th scanning line in M ​​scanning cycles to obtain the synthesized data on the i-th scanning line in one image generation cycle", the formula for obtaining the synthesized data is: Dataout f1 new(I)=-Dataout f1 (I)+(Dataout f1 A(I)+Dataout f1 B(I))*0.5 Among them, Dataout f1 new(I) is the synthetic data on the i-th scan line in an image generation cycle, Dataout f1 (I) is the first target scanning data corresponding to the i-th scanning line in the first scanning cycle, Dataout f1 A(I) is the first target scanning data corresponding to the i-th scanning line in the second scanning cycle, Dataout f1 B(I) is the first target scanning data corresponding to the i-th scanning line in the second scanning cycle, and the first scanning cycle, the second scanning cycle and the third scanning cycle belong to the same image generation cycle.

10. The method according to claim 1, characterized in that The method further comprises: Determine second target scanning data corresponding to the i-th scanning line in M ​​scanning cycles based on historical scanning data acquired by the second ultrasonic probe on at least two adjacent scanning lines, wherein the first ultrasonic probe and the second ultrasonic probe have different frequencies of transmitting ultrasonic waves; Synthesize the second target scanning data corresponding to the i-th scanning line in M ​​scanning cycles to obtain synthesized data on the i-th scanning line in one image generation cycle, wherein one image generation cycle includes M scanning cycles, and M and N are both positive integers; Based on the synthetic data of the second ultrasonic probe on N scanning lines in one image generation cycle, a frame of second ultrasonic image corresponding to one image generation cycle is generated, and the second ultrasonic image is a 360-degree annular grayscale image.

11. The method according to claim 10, characterized in that The first ultrasound image and the second ultrasound image are generated simultaneously, The method further comprises: Based on the set display mode, the first ultrasound image and the second ultrasound image are displayed.

12. The method according to claim 11, characterized in that The display modes include single-frame switching display, dual-frame same-screen display and dual-frame fusion display; When the display mode is the dual-image fusion display, the displaying of the first ultrasound image and the second ultrasound image includes: When the first ultrasonic image and the second ultrasonic image are received, the first ultrasonic image and the second ultrasonic image generated in the same image generation cycle are fused to obtain a fused image; The fused image is displayed.

13. An electronic device comprising: at least one processor; And a memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor so that the at least one processor can execute the ultrasound image generation method as described in any one of claims 1 to 12.

14. A non-transitory computer-readable storage medium storing computer instructions, wherein: The computer instructions are used to enable the computer to execute the ultrasound image generating method according to any one of claims 1 to 12.

15. A computer program product, comprising a computer program, wherein when the computer program is executed by a processor, the computer program implements the ultrasound image generating method according to any one of claims 1 to 12.

Images