An ultrafast ultrasound imaging method and system that fuses edge waves

Abstract

The application discloses a kind of based on fusion edge wave's superfast ultrasonic imaging method and system, belong to ultrasonic imaging technical field.First, the basic parameters of ultrasonic imaging and probe transmitting-receiving aperture are configured, and the echo data of plane wave / divergent wave and edge wave are collected;For plane wave / divergent wave echo data, conventional delay beam forming processing is used, for edge wave echo data, independent delay calculation and beam forming are completed using exclusive delay algorithm, and two types of image sets are obtained respectively.Combining the coverage range of ultrasonic emission sound field, aperture position and emission angle, construct distance negative correlation weighted space mask matrix, use mask matrix to weight each sub-image, finally, all weighted sub-images are coherently synthesized, and the ultrasonic imaging result is output.The application can effectively make up the signal missing defect under the scene of probe array element shielding, suppress edge wave imaging artifact, and significantly improve the ultrasonic imaging quality of shielding area.

Description

Technical Field

[0001] This invention belongs to the field of ultrasound imaging technology, and particularly relates to medical ultrasound synthetic aperture imaging and ultrafast ultrasound imaging technology, specifically an ultrafast ultrasound imaging method and system based on fused edge waves. Background Technology

[0002] Ultrasound imaging, with its advantages of being non-invasive and radiation-free, having good real-time performance, being easy to operate, and being inexpensive, has become one of the most widely used imaging technologies in clinical medical diagnosis and intraoperative monitoring. Ultrafast ultrasound imaging, by emitting planar or divergent waves, can achieve frame rates far exceeding those of traditional focused imaging, and has outstanding application value in cutting-edge fields such as blood flow imaging and elastography.

[0003] Current mainstream ultrafast imaging technologies are all designed based on the ideal scenario of the probe operating effectively across its entire aperture, without considering the common problem of probe element obstruction in clinical practice. In actual clinical applications, probe element obstruction is very common: for example, during cardiac or liver imaging, bone structures may obstruct part of the probe elements; or there may be localized damage to the probe elements, or the need to limit aperture usage in special imaging scenarios. All of these situations can prevent certain areas of the probe elements from transmitting and receiving ultrasound waves normally. In such cases, relying solely on conventional multi-plane wave composite imaging cannot effectively cover the imaging field of view corresponding to the obstructed area, causing a sharp drop in the signal-to-noise ratio of the echo signal in that area, severely impairing imaging resolution and contrast, and even making it impossible to obtain effective diagnostic images.

[0004] This invention proposes edge wave imaging using the edge wave sound field emitted by the edge array elements of the probe. This can supplement the sound field in areas that cannot be covered by traditional plane waves, thereby improving the echo signal intensity in those areas to some extent. However, considering that edge wave imaging alone has inherent defects such as severe imaging artifacts and a low main-side lobe ratio, and also increases the number of acquisitions and reduces the frame rate, it cannot meet the core requirements of clinical diagnosis for imaging quality. Therefore, it is necessary to perform composite imaging of plane waves and edge waves on the echo data to suppress various wavefront artifacts.

[0005] Regarding the solution proposed in this invention, there is currently no mature solution in the prior art that effectively fuses plane wave imaging and enhanced edge wave imaging. To address the aforementioned deficiencies in the prior art, this invention proposes an ultrafast ultrasound imaging method based on fused edge waves. Summary of the Invention

[0006] To address the shortcomings of existing technologies, this invention proposes an ultrafast ultrasound imaging method that integrates edge waves.

[0007] One of the above-mentioned objectives of the present invention is achieved by the following technical solution: An ultrafast ultrasound imaging method based on fused edge waves includes the following steps: Step 1: Configure the core basic parameters of ultrasound imaging and complete the setting of the transceiver aperture of the ultrasound probe to provide basic parameter support for ultrasound signal transmission and data acquisition; Step 2: Based on the set probe transmit and receive apertures, transmit two types of ultrasonic signals: plane wave / divergent wave and edge wave, and simultaneously acquire the corresponding ultrasonic echo signals to obtain two types of raw echo data; Step 3: Build a GPU-based parallel acceleration plane wave / divergent wave imaging technology framework. For the two types of echo data, plane wave / divergent wave and edge wave, a differentiated GPU-accelerated beamforming method is used to perform parallel computation processing to obtain the corresponding plane wave / divergent wave sub-image and edge wave sub-image. Step 4: Based on the two types of sub-images obtained in Step 3, construct a spatial mask matrix with inverse distance weighting. The main process is to set corresponding weight values ​​for the effective coverage area, transition area, and area exceeding the coverage threshold of the sound field according to the coverage range of the emitted sound field of the plane wave / divergent wave and the edge wave, the position of the emission aperture, and the emission angle. For different emission angles, the angle parameters in the above process are instantiated, and a specific mask matrix corresponding to each sub-image is calculated and generated, thereby forming a mask matrix set that serves subsequent image reconstruction. Step 5: Using the corresponding mask matrix in the mask matrix set, weight the sub-images in the plane wave / divergent wave sub-image set and the edge wave sub-image set, coherently synthesize all the weighted sub-images, and obtain the final ultrasound imaging result after normalization and dynamic range adjustment.

[0008] Furthermore, in step 1: the basic parameters of ultrasound imaging include emission frequency, sampling rate, imaging depth, emission angle range, and number of imaging frames.

[0009] Further, in step 1: the setting of the transceiver aperture of the ultrasonic probe includes: according to the preset probe array element blocking area, dividing the effective transmitting array elements of the probe into two groups of transmitting sub-apertures, corresponding to the left and right sides of the blocking area respectively, and simultaneously setting the receiving aperture, shielding the array elements in the blocking area, and retaining only the effective array elements for receiving the echo signal.

[0010] Further, step 2 includes: based on the configured imaging parameters, emitting multiple plane waves or several divergent waves with different deflection angles through two sets of emitter sub-apertures, and simultaneously emitting enhanced edge waves adapted to the occlusion area.

[0011] Furthermore, step 2 includes: during the transmission process, according to the positive and negative values ​​and zero values ​​of the current transmission angle, using a linear, exponential, or Tukey window function to weight and adjust the amplitude of the transmission aperture, thereby enhancing the edge wave transmission efficiency at the corresponding angle and improving the sound field coverage effect of the obstructed area.

[0012] Furthermore, step 2 includes: for each ultrasonic transmission event, acquiring the corresponding ultrasonic echo radio frequency data through the set receiving aperture, and completing the echo data acquisition for all transmission events.

[0013] Furthermore, the processing of plane wave / divergent wave echo radio frequency data in step 3 includes: first, the CPU performs vectorization preprocessing of multi-channel radio frequency signals to obtain complex signals, which are then transmitted to the GPU. Then, conventional GPU-accelerated delay superposition beamforming processing is used to ensure the imaging quality of the effective aperture area, and finally, plane wave / divergent wave image sets corresponding to different emission angles are obtained.

[0014] Furthermore, the processing of edge wave echo RF data in step 3 includes: first, establishing a physical model of the edge wave, equating the edge wave generated at the aperture edge during plane wave / divergent wave transmission to a spherical wave emitted by a virtual point source at the aperture edge; then, dynamically adjusting the transmission delay of the virtual point source according to the transmission angle, calculating the dedicated transmission delay and reception delay for each imaging pixel; and finally, using a dedicated delay algorithm combining plane wave / divergent wave and edge spherical wave to complete the delay calculation and beamforming, ultimately obtaining edge wave image sets corresponding to different transmission angles.

[0015] Furthermore, in step 4, the method for implementing the distance-negative correlation weighted spatial mask matrix is ​​as follows: first, calculate the lateral boundary of the sound field coverage of plane wave / divergent wave and edge wave at each imaging depth; set the highest weight for pixels within the effective sound field coverage area; for pixels outside the sound field coverage area, calculate the weight in the inverse distance method according to their vertical distance to the nearest sound field boundary, and set the weight of pixels whose distance exceeds the preset threshold to zero.

[0016] The second objective of this invention is achieved through the following technical solution: An ultrasound imaging system based on the synthesis of edge waves and plane / divergent waves, used to implement the above-mentioned ultrafast ultrasound imaging method based on fused edge waves, includes: The parameter configuration module is used to configure the core basic parameters of ultrasound imaging and to complete the planning and setting of the probe's transmitting and receiving apertures. The transmission and acquisition module is used to control the probe to emit plane waves / divergent waves and enhanced edge waves by using differentiated window functions according to the transmission angle, and to simultaneously acquire the corresponding ultrasonic echo radio frequency data; The beamforming module is used to perform GPU-accelerated conventional delay superposition beamforming on plane wave / divergent wave echoes, and to perform GPU-accelerated independent beamforming on edge wave echoes using a dedicated delay algorithm that combines plane wave / divergent wave with edge spherical wave, respectively obtaining plane wave / divergent wave sub-image sets and edge wave sub-image sets. The mask construction module is used to construct a set of distance-inverse weighted spatial mask matrices based on sound field coverage; The image synthesis module is used to perform weighted processing on each image using a mask matrix, and outputs the final ultrasound image after coherent synthesis.

[0017] The advantages and positive effects of this invention are as follows: This invention improves upon existing multiplane wave / divergent wave ultrasound imaging technology. By optimizing the transmitter window function, optimizing the receiver-specific delay algorithm, and combining a mask-weighted image synthesis strategy, it effectively solves the imaging problem in scenarios where ultrasound probe array elements are obstructed. It possesses multiple technical advantages and beneficial effects, as detailed below: 1. This invention relies on an edge wave-specific delay algorithm to fill in the sound field defects in the obstructed area and optimize the imaging quality. It can accurately supplement the sound field in the probe obstructed area that cannot be covered by traditional plane wave / divergent wave, effectively improving the echo signal intensity in the obstructed area. At the same time, it combines window function to enhance the edge wave emission performance and mask weighted synthesis strategy to effectively suppress edge wave imaging artifacts, completely improving the problems of signal loss and severe imaging artifacts in the obstructed area in traditional technology.

[0018] 2. This invention can balance imaging accuracy and ultra-high frame rate, and has excellent imaging efficiency. It does not require additional ultrasonic wave transmissions. While achieving high-definition imaging in obstructed areas and optimizing the overall imaging effect, it fully retains the high frame rate advantage of ultra-fast ultrasonic imaging. It perfectly adapts to the real-time and fast ultrasonic imaging requirements in obstructed scenarios and solves the technical contradiction that traditional methods require sacrificing imaging speed to improve imaging quality.

[0019] 3. This invention effectively improves the ultrasonic obstruction imaging technology system, fills the gap in related technologies in the industry, and specifically adapts to the special imaging conditions of probe array element obstruction. It constructs a dedicated imaging optimization system and quantitative evaluation scheme, fills the gap in the industry for a dedicated quantitative evaluation scheme for the imaging quality of ultrasonic obstruction areas, and breaks through the limitations of traditional ultrasonic imaging technology in adapting to complex obstruction scenarios.

[0020] 4. This invention has strong practicality and adaptability, and its application scenarios are very wide. The imaging method has a simple structure and high computational efficiency. It is compatible with conventional ultra-fast ultrasonic imaging equipment, requires no additional hardware modification, and can be widely applied to various ultrasonic testing scenarios with array element obstruction. It has strong engineering application value and promotion potential. Attached Figure Description

[0021] Figure 1 This is a flowchart illustrating the overall process of the ultrasound imaging method described in this invention. Figure 2 This is a schematic diagram of the ultrasonic probe blocking area and the emission stage in an embodiment of the present invention; Figure 3 A schematic diagram of the angle-differentiated window function described in this invention; (a) an exponentially rising window function with the right channel closed (index 1 to 50 is the rising edge of the exponent, and index 51 to 128 is set to zero and closed); (b) an exponentially falling window function with the left channel closed (index 1 to 78 is set to zero and closed, and index 79 to 128 is the falling edge of the exponent). Figure 4 The following are diagrams illustrating the use of plane waves in the occlusion scenario of this invention: (a) a grayscale image in B mode; (b) a one-dimensional transverse profile curve taken at a depth of 20 mm, with the horizontal axis representing the transverse position (mm) and the vertical axis representing the normalized amplitude; (c) a one-dimensional longitudinal profile curve taken at a transverse position of 0 mm, with the horizontal axis representing the depth position (mm) and the vertical axis representing the normalized amplitude. Figure 5 The following is an illustration of the effect of using plane wave and edge wave fusion under occlusion conditions according to the present invention: (a) B-mode grayscale image; (b) a one-dimensional transverse profile curve taken at a depth of 20 mm, with the horizontal axis representing the transverse position (mm) and the vertical axis representing the normalized amplitude; (c) a one-dimensional longitudinal profile curve taken at a transverse position of 0 mm, with the horizontal axis representing the depth position (mm) and the vertical axis representing the normalized amplitude. Detailed Implementation

[0022] The structure of the present invention will be further described below with reference to the accompanying drawings and embodiments.

[0023] This embodiment provides an ultrafast ultrasound imaging method based on edge wave fusion. Simulated using the FieldII ultrasound simulation platform, it is adaptable to applications such as intraoperative ultrasound in clinical settings and ultrasound imaging under conditions of partial probe element failure. Without increasing hardware system complexity, it effectively solves the problem of signal loss in the imaging area due to probe element occlusion, while simultaneously suppressing edge wave imaging artifacts. This invention uses a plane wave ultrafast ultrasound imaging method based on edge wave fusion as an example to illustrate its specific implementation, which includes the following steps: Step 1: Complete the simulation environment setup and basic parameter configuration.

[0024] First, configure the simulation tool environment by adding the FieldII simulation toolkit path and setting the simulation data save path. Then, configure the core basic parameters for ultrasound imaging, including simulation signal-to-noise ratio, imaging depth range, plane wave emission angle range and number of angles, number of imaging frames, and sampling rate. Next, configure the core parameters for the ultrasound linear array probe, including center frequency, number of array elements, element spacing, and focusing depth. Finally, based on the preset obstruction area, set the transceiver apertures: set the probe's central area as the obstruction area, dividing it into two sets of transmitting sub-apertures, corresponding to the two sides of the obstruction area, respectively. The receiving aperture shields the array elements in the obstruction area, retaining only the effective array elements for echo signal reception.

[0025] In this embodiment, the simulated signal-to-noise ratio is set to 1000, the initial imaging depth is 0mm, the maximum imaging depth is 40mm, the plane wave emission angle range is -10° to +10°, the number of emission angles is 3, the number of imaging frames is 1, and the sampling rate is 4 times the emission frequency. The ultrasonic linear array probe is a 128-element linear array probe with a center frequency of 7.5MHz and an element spacing of 0.3mm. The obstruction area is set at the center of the probe, with elements 50 to 79. The left transmitting sub-aperture has effective elements 1 to 49, and the right transmitting sub-aperture has effective elements 80 to 128. The receiving aperture is consistent with the effective elements of the transmitting sub-aperture.

[0026] This embodiment uses point target phantoms, setting two sets of point targets at different lateral positions, distributed at equal intervals along the imaging depth direction. Each point target is assigned a corresponding scattering amplitude, which is used for subsequent evaluation of imaging resolution and main lobe-to-side lobe ratio.

[0027] In this embodiment, the first group of point targets are located at depths of 10mm, 15mm, 20mm, 25mm, and 30mm, respectively, with corresponding scattering amplitudes of 1, 0.5, 0.1, 0.05, and 0.005. The second group of point targets is the first group of point targets shifted 10mm to the left laterally, and the depth distribution and scattering amplitude are completely consistent with the first group.

[0028] Step 2: Complete the acquisition of ultrasonic emission and echo data.

[0029] First, multiple different emission angles are set, corresponding to the plane wave emission and edge wave emission of the left and right sets of emission sub-apertures, respectively. Before each emission, the emission aperture is weighted by the corresponding window function according to the positive, negative and zero values ​​of the current emission angle, thereby enhancing the edge wave emission at the corresponding angle. Then, through the ultrasonic simulation platform, the corresponding emission sub-aperture is matched for each set of emission angles, and the window function is applied to each emission sub-aperture to complete the simulation acquisition of ultrasonic emission and echo data, and plane wave echo data and edge wave echo data are obtained respectively.

[0030] In this embodiment, a total of 4 sets of emission angles are set, corresponding to the plane wave emission of the left emission sub-aperture, the plane wave emission of the right emission sub-aperture, the edge wave emission of the left emission sub-aperture, and the edge wave emission of the right emission sub-aperture, respectively. The windowing function is specifically as follows: when the emission angle is greater than 0, an exponentially rising apodization function is used to enhance the emission of the right edge of the aperture; when the emission angle is less than 0, an exponentially falling apodization function is used to enhance the emission of the left edge of the aperture; when the emission angle is 0, a Tukey window apodization function with a parameter of 0.5 is used to smooth the emission of the aperture edge.

[0031] Step 3: Echo Data Beamforming First, configure the core parameters of GPU beamforming, including imaging pixel range, sound velocity, sampling rate, etc. Based on the CUDA architecture, construct two types of parallel beamforming kernels, corresponding to conventional delay superposition beamforming for plane waves and dedicated hybrid delay beamforming for edge waves, respectively. For edge wave echo data, first dynamically set the position of the virtual edge point source according to the transmission angle, then call the dedicated edge wave beamforming kernel to calculate the spherical wave transmission delay and reception delay for each imaging pixel, complete the delay alignment and coherent superposition, and obtain the edge wavelet image.

[0032] In this embodiment, the position of the virtual point source of the edge wave is dynamically adjusted according to the emission angle. When emitting at a negative angle, the virtual point source is set at the left edge of the emission sub-aperture, and when emitting at a positive angle, the virtual point source is set at the right edge of the emission sub-aperture near the obstruction area.

[0033] Step 4: Complete the construction of the inverse distance weighted mask. By setting a distance threshold and a weighting function, for each sub-image of the emission angle, the lateral boundary of the sound field coverage at each imaging depth is calculated. All imaging pixels are traversed, and the corresponding mask weight values ​​are calculated based on the positional relationship between the pixels and the sound field boundary, thus forming a mask matrix set corresponding to the sub-image set. At the same time, the constructed mask matrix is ​​visualized and verified to ensure that the weight distribution conforms to the actual situation of the sound field coverage.

[0034] In this embodiment, the distance threshold is set to 5mm, and the weight function adopts the reciprocal function, specifically weight=1 / (1+9min_distance / distance_threshold), where min_distance is the vertical distance from the pixel to the nearest sound field boundary; the mask weight assignment rule is: the pixel weight within the effective sound field coverage area is assigned a weight of 1, the pixel weight exceeding the threshold is assigned a weight of 0, and the pixel weight in the transition area is calculated according to the inverse distance function.

[0035] Step 5: Complete the mask weighting and synthetic imaging of the sub-images.

[0036] Using the constructed mask matrix set, the corresponding planar wavelet images and edge wavelet images are weighted at the pixel level. Then, all the weighted sub-images are coherently synthesized. The synthesized image is then normalized in amplitude and logarithmically compressed. After adjusting the dynamic range, the final B-mode ultrasound image is obtained.

[0037] In this embodiment, coherent synthesis adopts a coherent superposition method. The pixel amplitude values ​​of all weighted sub-images are superimposed, divided by the total number of sub-images to complete amplitude normalization, and then logarithmic compression is performed. The imaging dynamic range is set to 50dB, and the final B-mode ultrasound image is output.

[0038] Finally, the constructed mask matrix, the final imaging results, and the amplitude profile of the point target are visualized, and all imaging data are saved to a preset path to complete the entire imaging process.

[0039] Through the above implementation process, this method achieves effective synthesis imaging of edge waves and plane waves. While improving the signal intensity in the occluded area, it effectively suppresses edge wave artifacts, providing a feasible solution for ultrasound clinical imaging in array element occlusion scenarios.

[0040] Furthermore, embodiments of the present invention also provide an ultrasound imaging system based on the synthesis of edge waves and plane waves / divergent waves, for implementing the above-mentioned ultrafast ultrasound imaging method based on fused edge waves, including: The parameter configuration module is used to configure the core basic parameters of ultrasound imaging and to complete the planning and setting of the probe's transmitting and receiving apertures. The transmission and acquisition module is used to control the probe to emit plane waves / divergent waves and enhanced edge waves by using differentiated window functions according to the transmission angle, and to simultaneously acquire the corresponding ultrasonic echo radio frequency data; The beamforming module is used to perform GPU-accelerated conventional delay superposition beamforming on plane wave / divergent wave echoes, and to perform GPU-accelerated independent beamforming on edge wave echoes using a dedicated delay algorithm that combines plane wave / divergent wave with edge spherical wave, respectively obtaining plane wave / divergent wave sub-image sets and edge wave sub-image sets. The mask construction module is used to construct a set of distance-inverse weighted spatial mask matrices based on sound field coverage; The image synthesis module is used to perform weighted processing on each image using a mask matrix, and outputs the final ultrasound image after coherent synthesis.

[0041] Although embodiments and drawings of the present invention have been disclosed for illustrative purposes, those skilled in the art will understand that various substitutions, variations and modifications are possible without departing from the spirit and scope of the present invention and the appended claims. Therefore, the scope of the present invention is not limited to the contents disclosed in the embodiments and drawings.

Claims

1. An ultrafast ultrasound imaging method based on fused edge waves, characterized in that: Includes the following steps: Step 1: Configure the core basic parameters of ultrasound imaging and complete the setting of the transceiver aperture of the ultrasound probe to provide basic parameter support for ultrasound signal transmission and data acquisition; Step 2: Based on the set probe transmit and receive apertures, transmit two types of ultrasonic signals: plane wave / divergent wave and edge wave, and simultaneously acquire the corresponding ultrasonic echo signals to obtain two types of raw echo data; Step 3: Build a GPU-based parallel acceleration plane wave / divergent wave imaging technology framework. For the two types of echo data, plane wave / divergent wave and edge wave, a differentiated GPU-accelerated beamforming method is used to perform parallel computation processing to obtain the corresponding plane wave / divergent wave sub-image and edge wave sub-image. Step 4: Based on the plane wave / divergent wavelet image and edge wavelet image output in Step 3, first combine the sound field coverage range, emission aperture position and emission angle of the two types of waveforms, and divide the sound field region according to the distance inverse weighting rule. Set the benchmark weights for the effective coverage area, transition area and area exceeding the coverage threshold respectively to obtain the general spatial mask construction standard; then substitute each set of emission angle parameters into the standard, calculate and generate an independent mask matrix matching the current emission angle for each sub-image, and summarize all mask matrices to form a mask matrix set; Step 5: Using the corresponding mask matrix in the mask matrix set, weight the sub-images in the plane wave / divergent wave sub-image set and the edge wave sub-image set, coherently synthesize all the weighted sub-images, and obtain the final ultrasound imaging result after normalization and dynamic range adjustment.

2. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: In step 1: the basic parameters of ultrasound imaging include emission frequency, sampling rate, imaging depth, emission angle range, and number of imaging frames.

3. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: In step 1, the setting of the transceiver aperture of the ultrasonic probe includes: dividing the effective transmitting array elements of the probe into two groups of transmitting sub-apertures according to the preset probe array element blocking area, corresponding to the left and right sides of the blocking area respectively, and setting the receiving aperture at the same time, shielding the array elements in the blocking area, and retaining only the effective array elements for receiving the echo signal.

4. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: Step 2 includes: based on the configured imaging parameters, emitting multiple plane waves or several divergent waves with different deflection angles through two sets of emitter sub-apertures, and simultaneously emitting enhanced edge waves adapted to the occlusion area.

5. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: Step 2 includes: during the launch process, using a linear, exponential, or Tukey window function to weight the amplitude of the launch aperture based on the sign and zero value of the current launch angle.

6. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: Step 2 includes: for each ultrasonic transmission event, acquiring the corresponding ultrasonic echo radio frequency data through the set receiving aperture, and completing the echo data acquisition for all transmission events.

7. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: The processing of plane wave / divergent wave echo radio frequency data in step 3 includes: first, the CPU performs vectorization preprocessing of multi-channel radio frequency signals to obtain complex signals, which are then transmitted to the GPU. Then, conventional GPU-accelerated delay superposition beamforming processing is used to ensure the imaging quality of the effective aperture area, and finally, plane wave / divergent wave image sets corresponding to different emission angles are obtained.

8. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: The processing of edge wave echo RF data in step 3 includes: first, establishing a physical model of the edge wave, equating the edge wave generated at the aperture edge during plane wave / divergent wave transmission to a spherical wave emitted by a virtual point source at the aperture edge; then, dynamically adjusting the transmission delay of the virtual point source according to the transmission angle, calculating the dedicated transmission delay and reception delay for each imaging pixel; and finally, using a dedicated delay algorithm combining plane wave / divergent wave and edge spherical wave to complete the delay calculation and beamforming, ultimately obtaining edge wave image sets corresponding to different transmission angles.

9. The ultrafast ultrasound imaging method based on fused edge waves according to claim 1, characterized in that: In step 4, the implementation method of the general spatial mask construction standard is as follows: first, calculate the lateral boundary of the sound field coverage of plane wave / divergent wave and edge wave at each imaging depth; and set the highest weight for pixels within the effective sound field coverage area. For pixels outside the sound field coverage area, the weight is calculated inversely based on the vertical distance to the nearest sound field boundary. Pixels whose distance exceeds a preset threshold are set to zero weight.

10. An ultrasound imaging system based on the synthesis of edge waves and plane waves / divergent waves, used to implement the ultrafast ultrasound imaging method based on fused edge waves as described in any one of claims 1-9, characterized in that, include: The parameter configuration module is used to configure the core basic parameters of ultrasound imaging and to complete the planning and setting of the probe's transmitting and receiving apertures. The transmission and acquisition module is used to control the probe to emit plane waves / divergent waves and enhanced edge waves by using differentiated window functions according to the transmission angle, and to simultaneously acquire the corresponding ultrasonic echo radio frequency data; The beamforming module is used to perform GPU-accelerated conventional delay superposition beamforming on plane wave / divergent wave echoes, and to perform GPU-accelerated independent beamforming on edge wave echoes using a dedicated delay algorithm that combines plane wave / divergent wave with edge spherical wave, respectively obtaining plane wave / divergent wave sub-image sets and edge wave sub-image sets. The mask construction module is used to construct a set of distance-inverse weighted spatial mask matrices based on sound field coverage; The image synthesis module is used to perform weighted processing on each image using a mask matrix, and outputs the final ultrasound image after coherent synthesis.

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