Ultrasound imaging method, apparatus, ultrasound device, and readable storage medium

Abstract

This application discloses an ultrasound imaging method, apparatus, ultrasound device, and computer-readable storage medium. The method includes: obtaining mask volume data based on ultrasound volume data with niche volume data removed; wherein the niche volume data is volume data corresponding to the niche region in the ultrasound image; determining the imaging mode corresponding to each position of the mask volume data on the ultrasound image; wherein the first imaging mode corresponding to the contact area between the mask volume data and the niche volume data is different from the second imaging mode corresponding to the non-contact area in the mask volume data; rendering each position on the ultrasound image using the mask volume data according to the imaging mode to obtain the ultrasound image; the ultrasound image generated by this method can simultaneously possess information provided by two imaging modes, increasing the information content of the ultrasound image.

Description

Technical Field

[0001] This application relates to the field of ultrasonic equipment technology, and in particular to an ultrasonic imaging method, an ultrasonic imaging device, an ultrasonic equipment, and a computer-readable storage medium. Background Technology

[0002] Currently, there are three methods for visualizing ultrasound data: volume rendering, surface rendering, and niche rendering. Among them, niche rendering images are created by imaging three mutually perpendicular cross-sections intersecting at a selected location in the form of a stereoscopic view. This imaging method can provide limited information. Summary of the Invention

[0003] In view of this, the purpose of this application is to provide an ultrasound imaging method, an ultrasound imaging device, an ultrasound equipment, and a computer-readable storage medium that increases the amount of information in ultrasound images.

[0004] To address the aforementioned technical problems, this application provides an ultrasound imaging method, comprising:

[0005] Mask volume data is obtained from ultrasound volume data after removing niche shadow volume data; wherein, the niche shadow volume data is the volume data corresponding to the niche shadow region in the ultrasound image;

[0006] The imaging mode corresponding to each position of the mask data on the ultrasound image is determined; wherein, the first imaging mode corresponding to the contact area between the mask data and the niche data is different from the second imaging mode corresponding to the non-contact area in the mask data.

[0007] According to the imaging method, the ultrasound image is obtained by rendering the various positions on the ultrasound image using the mask data.

[0008] Optionally, obtaining mask volume data from the ultrasound volume data based on the removed niche shadow volume data includes:

[0009] Acquire ultrasound body data corresponding to ultrasound images;

[0010] Obtain niche body information corresponding to the niche region in the ultrasound image, and separate and delete the niche body data corresponding to the niche body information from the ultrasound body data;

[0011] The ultrasonic body data from which the niche shadow data is separated and deleted is determined as the mask body data.

[0012] Optionally, acquiring ultrasound body data corresponding to the ultrasound image includes:

[0013] Obtain raw ultrasound body data;

[0014] Obtain valid data range information, and determine the valid data corresponding to the valid data range information in the original ultrasound body data;

[0015] The ultrasound body data is obtained based on the valid data in the original ultrasound body data.

[0016] Optionally, the niche shadow information includes niche shadow coordinates and quadrant designation information;

[0017] The process of separating and deleting the niche data corresponding to the niche information from the ultrasound body data includes:

[0018] Construct three planes; the three planes are perpendicular to each other in every pair, and the coordinates of the intersection of the three planes are the coordinates of the niche shadow body;

[0019] The ultrasound body data is segmented according to the plane to obtain multiple ultrasound body quadrant data;

[0020] The target ultrasound body quadrant data corresponding to the quadrant specified information is determined as the niche shadow body data and deleted.

[0021] Optionally, determining the imaging mode corresponding to each position of the mask data on the ultrasound image includes:

[0022] Determine the imaging direction;

[0023] Based on the imaging direction, the imaging method corresponding to each position of the mask data on the ultrasound image is determined.

[0024] Optionally, determining the imaging method corresponding to each position of the mask data on the ultrasound image based on the imaging direction includes:

[0025] Construct a two-dimensional template perpendicular to the imaging direction;

[0026] Along the imaging direction, the mask data is projected onto the two-dimensional template;

[0027] The identification information corresponding to the first position on the two-dimensional template is set as the first mode information corresponding to the first imaging mode; wherein, the area to which the projection point corresponding to the first position belongs on the mask data is the contact area;

[0028] The identification information corresponding to the second position on the two-dimensional template is set as the second mode information corresponding to the second imaging mode; wherein, the area to which the projection point corresponding to the second position belongs on the mask data is the non-contact area;

[0029] Based on the identification information of the first and second positions in the two-dimensional template, the imaging mode of the ultrasound image is determined.

[0030] Optionally, the step of rendering the ultrasound image at each location using the mask data according to the imaging method to obtain the ultrasound image includes:

[0031] Based on the identification information of the first position and the second position, a first rendering area corresponding to the first method information and a second rendering area corresponding to the second method information on the ultrasound image are determined;

[0032] A first image is obtained by rendering the first image in the first rendering area based on the first imaging method;

[0033] A second image is obtained by rendering in the second rendering area based on the second imaging method;

[0034] The ultrasound image is composed of the first image and the second image.

[0035] Optionally, the first imaging method includes a volume rendering method;

[0036] The step of rendering the first image in the first rendering area based on the first imaging method to obtain the first image includes:

[0037] In the first rendering area, along the imaging direction, the mask volume data is rendered using the volume rendering method to obtain the first image.

[0038] Optionally, the first imaging method includes a ray projection rendering method based on the target projection thickness;

[0039] The step of rendering the first image in the first rendering area based on the first imaging method to obtain the first image includes:

[0040] Obtain target projection thickness information;

[0041] Based on the target projection thickness information, determine the light stopping point corresponding to the light projection along the imaging direction;

[0042] In the first rendering area, the mask data is rendered based on the light stopping point using the light projection rendering method to obtain the first image.

[0043] Optionally, the target projection thickness information includes the sampling point interval and the number of sampling points;

[0044] The step of determining the ray stopping point corresponding to the ray projection along the imaging direction based on the target projection thickness information includes:

[0045] The final sampling point distance is obtained using the sampling point interval and the number of sampling points;

[0046] Along the imaging direction, starting from the two-dimensional template, a point whose distance from the starting point is equal to the distance from the final sampling point is selected as the light stopping point.

[0047] Optionally, the first imaging method includes a cross-sectional rendering method;

[0048] The step of rendering the first image in the first rendering area based on the first imaging method to obtain the first image includes:

[0049] The projection image of the contact area of ​​the mask data onto the two-dimensional template along the imaging direction is determined as the first image.

[0050] Optionally, the second imaging method includes a volume rendering method;

[0051] The step of rendering the second image in the second rendering area based on the second imaging method to obtain the second image includes:

[0052] In the second rendering area, along the imaging direction, the mask volume data is rendered using the volume rendering method to obtain the second image.

[0053] Optionally, the second imaging method includes a surface rendering method;

[0054] The step of rendering the second image in the second rendering area based on the second imaging method to obtain the second image includes:

[0055] The projection image of the non-contact area of ​​the mask data onto the two-dimensional template along the imaging direction is determined as the second image.

[0056] This application also provides an ultrasound imaging device, comprising:

[0057] The mask volume acquisition module is used to obtain mask volume data based on ultrasound volume data after removing niche shadow volume data; wherein, the niche shadow volume data is the volume data corresponding to the niche shadow region in the ultrasound image;

[0058] The mode determination module is used to determine the imaging mode corresponding to each position of the mask data on the ultrasound image; wherein, the first imaging mode corresponding to the contact area between the mask data and the niche data is different from the second imaging mode corresponding to the non-contact area in the mask data.

[0059] The generation module is used to render the ultrasound image at each position on the ultrasound image using the mask data according to the imaging method, so as to obtain the ultrasound image.

[0060] This application also provides an ultrasonic device, including a memory and a processor, wherein:

[0061] The memory is used to store computer programs;

[0062] The processor is used to execute the computer program to implement the ultrasound imaging method described above.

[0063] This application also provides a computer-readable storage medium for storing a computer program, wherein the computer program, when executed by a processor, implements the above-described ultrasound imaging method.

[0064] The ultrasound imaging method provided in this application obtains mask volume data based on ultrasound volume data with niche shadow data removed; wherein, the niche shadow data is the volume data corresponding to the niche shadow region in the ultrasound image; the imaging mode corresponding to each position of the mask volume data on the ultrasound image is determined; wherein, the first imaging mode corresponding to the contact area between the mask volume data and the niche shadow data is different from the second imaging mode corresponding to the non-contact area in the mask volume data; according to the imaging mode, the mask volume data is used to render each position on the ultrasound image to obtain the ultrasound image.

[0065] As can be seen, this method employs two different imaging techniques for rendering ultrasound images. Mask volume data is obtained by removing niche volume data from the ultrasound volume data. There is a contact area between the mask volume data and the niche volume data; this contact area is the region displayed during niche imaging. The generation of ultrasound volume data with the niche volume data removed allows the mask volume data to achieve niche imaging using the contact area. The contact and non-contact areas on the mask volume data are projected onto different positions in the ultrasound image. To enrich the ultrasound image with more information, different imaging techniques—a first imaging technique and a second imaging technique—are set for the contact and non-contact areas respectively. Ultrasound imaging is performed at each position using the corresponding imaging technique, resulting in an ultrasound image that incorporates information from both imaging techniques. This allows the generated ultrasound image to simultaneously possess information from both imaging techniques, increasing the information content of the ultrasound image.

[0066] In addition, this application also provides an ultrasound imaging device, an ultrasound equipment, and a computer-readable storage medium, which also have the above-mentioned beneficial effects. Attached Figure Description

[0067] To more clearly illustrate the technical solutions in the embodiments of this application or related technologies, the drawings used in the description of the embodiments or related technologies will be briefly introduced below. Obviously, the drawings described below are only embodiments of this application. For those skilled in the art, other drawings can be obtained based on the provided drawings without creative effort.

[0068] Figure 1 A flowchart of an ultrasound imaging method provided in this application embodiment;

[0069] Figure 2 A three-dimensional schematic diagram of specific mask body data provided in this application embodiment;

[0070] Figure 3 This is a schematic diagram of a two-dimensional template setting provided in an embodiment of this application;

[0071] Figure 4 This is a schematic diagram illustrating the principle of light projection imaging provided in an embodiment of this application;

[0072] Figure 5 A schematic diagram of an ultrasound image provided for an embodiment of this application;

[0073] Figure 6 This is another schematic diagram of an ultrasound image provided in an embodiment of this application;

[0074] Figure 7 A flowchart of a specific ultrasound imaging method provided in this application embodiment;

[0075] Figure 8 This is a schematic diagram of the structure of an ultrasound imaging device provided in an embodiment of this application;

[0076] Figure 9 This is a schematic diagram of the structure of an ultrasonic device provided in an embodiment of this application. Detailed Implementation

[0077] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the scope of protection of this application.

[0078] It should be noted that the ultrasound imaging method provided in this application can be performed by a specified electronic device, and the specific number of specified electronic devices is not limited; for example, there can be one or more. Specifically, if there is one electronic device, it can be an ultrasound device. If there are multiple electronic devices, in addition to the ultrasound device, the electronic devices may also include data acquisition devices (such as ultrasound probe devices) and other devices. The various electronic devices cooperate with each other to complete the ultrasound imaging.

[0079] For details, please refer to Figure 1 , Figure 1A flowchart illustrating an ultrasound imaging method provided in this application embodiment. The method includes:

[0080] S101: Obtain mask volume data based on ultrasound volume data after removing niche shadow volume data.

[0081] Ultrasound volume data refers to volume data used for ultrasound imaging. The specific methods for acquiring this data are not detailed here; please refer to relevant technologies. Ultrasound volume data can be acquired in advance or in real-time. For example, the ultrasound device can communicate with the ultrasound probe device to acquire the raw data sent by the probe device in real time, and use this raw data as the ultrasound volume data. In another implementation, because the three-dimensional spatial region corresponding to the raw data is relatively large, while the observed object, such as a lesion, is usually small, some data in the raw data has no practical use and may even provide invalid information. In this case, this invalid data can be removed, and the raw data remaining after removing the invalid data can be used as the ultrasound volume data.

[0082] In this application, mask volume data is obtained from ultrasound volume data with niche shadow data removed. The niche shadow data refers to the volume data corresponding to the niche region in the ultrasound image. It is understood that to achieve the niche shadow imaging effect, the original ultrasound volume data needs to be segmented to remove the niche shadow data. Ultrasound volume data with the niche shadow data removed can be directly used as mask volume data. Alternatively, in another embodiment, a region of interest can be further defined in the ultrasound volume data with the niche shadow data removed, and the ultrasound volume data within the region of interest can be determined as mask volume data. Specifically, in one embodiment, the process of obtaining mask volume data may include:

[0083] Step 11: Obtain ultrasound body data corresponding to the ultrasound image.

[0084] In an optional embodiment, ultrasound volume data corresponding to the ultrasound image can be obtained based on three-dimensional ultrasound technology. Three-dimensional ultrasound technology refers to ultrasound detection technology capable of three-dimensional imaging; the data acquired is volume data, which enables three-dimensional imaging and allows observation from any angle in space.

[0085] Step 12: Obtain the niche body information corresponding to the niche region in the ultrasound image, and separate and delete the niche body data corresponding to the niche body information from the ultrasound body data.

[0086] Step 13: Identify the ultrasonic body data from which the niche shadow data has been separated and deleted as mask body data.

[0087] Niche imaging refers to selecting a coordinate point within the ultrasound volume data as the intersection of three mutually orthogonal planes. These three planes are then used as cross-sections to cut through the ultrasound volume data, and the data from these cross-sections is used to create an image, allowing for a three-dimensional view of these three cross-sections. While this imaging method can capture more information about the internal structure of the lesion tissue, it loses a significant amount of other information, resulting in a relatively low overall information carrying capacity.

[0088] Understandably, when selecting points and performing cross-sectional observations within ultrasound body data, to observe the specific internal cross-section, the portion of the ultrasound body data segmented by the cross-section in the observation direction needs to be discarded. This discarded data is the niche shadow data. Niche shadow information describes the specific location of the niche shadow data within the ultrasound body data, and users can set the niche shadow information according to the desired cross-sectional location.

[0089] After obtaining the niche shadow information, the corresponding niche shadow data can be located in the ultrasound body data and separated and deleted from the ultrasound body data, thus discarding the niche shadow data. The remaining data can be called mask data. The specific deletion method is not limited; for example, all niche shadow data can be set to 0.

[0090] In one implementation, the niche information includes niche coordinates and quadrant designation information. Based on this, the process of separating and deleting the niche data corresponding to the niche information from the ultrasound data may include:

[0091] Step 21: Construct three planes.

[0092] Step 22: Segment the ultrasound body data according to the plane to obtain multiple ultrasound body quadrant data.

[0093] Step 23: Determine the target ultrasound body quadrant data corresponding to the quadrant specified information as the niche shadow body data and delete it.

[0094] In this system, the three planes are mutually perpendicular, and the coordinates of their intersection point represent the niche body coordinates. Based on these niche body coordinates, the ultrasound body data is segmented using these three planes into eight independent quadrants, each located within one of the eight quadrants of the Cartesian coordinate system to which the three planes belong. Quadrant designation refers to the specific quadrant within which the niche body data is located. The specific format is not limited; for example, it can be a quadrant number, such as 1 representing the first quadrant. By identifying the quadrant to which the niche body data belongs, it can be determined using the general quadrant identification method of the Cartesian coordinate system, and then deleted to obtain the mask body data.

[0095] In one implementation, specifically, the process of acquiring ultrasound body data may include:

[0096] Step 31: Obtain raw ultrasound body data.

[0097] Step 32: Obtain the valid data range information and determine the valid data corresponding to the valid data range information in the original ultrasound body data.

[0098] Step 33: Obtain ultrasound body data based on the valid data in the original ultrasound body data.

[0099] Raw ultrasound data refers to ultrasound data directly acquired by an ultrasound data acquisition device. This data can be acquired in real-time or pre-acquired and stored, and retrieved when imaging is required. The ultrasound data acquisition device can be an ultrasound machine.

[0100] Valid data range information refers to information used to specify valid data, and its specific form is not limited. Valid data range information can be obtained through preset or real-time acquisition methods. Specifically, it can indicate a sphere, cube, cubic, cylinder, prism, or irregular three-dimensional spatial range as the spatial range in which the valid data resides. The specific form of valid data range information is not limited; for example, it can be related to the form of its corresponding three-dimensional spatial range. For instance, when the three-dimensional spatial range is sphere, the valid data range information can be the spatial coordinates of the sphere's center and the sphere's radius. Or, when the three-dimensional spatial range is cube, the valid data range information can be the cube's center coordinates, length, width, and height. The specific content of the valid data range information can be set as needed. Depending on the area the user wants to focus on, its specific content will differ; for example, the coordinate values ​​of the sphere's center or the length of the sphere's radius may vary.

[0101] Based on the valid data range information, valid data within the three-dimensional spatial range defined by the valid data range information can be identified in the original ultrasound body data. Other data that does not belong to the valid data range can be considered invalid data. All valid data are used to construct the ultrasound body data.

[0102] Please refer to Figure 2The outermost cube (cube number 1) marks the extent of the initial ultrasound body data in three-dimensional space. The middle cube (cube number 2) marks the ultrasound body data (l2) consisting of valid data after the deletion of invalid data (l0), which is also in cube form. One corner of this ultrasound body data is cut out and deleted; this deleted part is the niche data (data within cube number 3). It can be seen that after the niche data is cut out and deleted, the ultrasound body data exposes three planes, i.e., cross-sections. These cross-sections are also the contact surfaces between the niche data and the mask data, and are marked as l1. Figure 2 The dimensions of the ultrasound body data shown are Xsrc*Ysrc*Zsrc, and the dimensions of the niche body data are Xniche*Yniche*Zniche.

[0103] S102: Determine the imaging method corresponding to each position of the mask data on the ultrasound image.

[0104] In this embodiment, the first imaging method corresponding to the contact area between the mask data and the niche data is different from the second imaging method corresponding to the non-contact area in the mask data. That is, the projection range of the contact area on the ultrasound image needs to be rendered using the first imaging method, while the projection range corresponding to the non-contact area needs to be rendered using the second imaging method. The contact area can be a plane, a curved surface, or other shapes. The non-contact area refers to the area in the mask data other than the contact area; specifically, it can be other surface areas of the mask data, or it can be the internal area of ​​the mask data. It should be noted that the specific forms of the first and second imaging methods in this application are not limited. Each imaging method can specify a corresponding rendering method, a color combination mode used during rendering, and a processing method for the obtained ultrasound image (e.g., visualization output display or storage in a specified storage location), etc., which can be set as needed. In one embodiment, if the niche imaging function is directly used, the rendering method specified by the first imaging method is a slice rendering method, specifically, the result of projecting the contact area onto the ultrasound image is directly used as the rendering result. Understandably, since mask volume data is also a type of ultrasound volume data, in another implementation, surface rendering or volume rendering can also be performed on the mask volume data; that is, the rendering method specified by the second imaging mode can be either surface rendering or volume rendering. Furthermore, in another implementation, if it is desired to provide more information from the niche imaging function, giving it depth information from the volume data, the first imaging mode can also be specified as volume rendering to further increase the depth information of the ultrasound volume data on top of the cross-sectional information. This type of rendering can be called niche volume rendering, i.e., a combination of niche rendering and volume rendering.

[0105] It is understandable that the mask data is capable of three-dimensional imaging, while the ultrasound image generated when observing this data is a two-dimensional image. Therefore, when generating the ultrasound image, the direction from which the mask data is observed can be determined; this direction is the imaging direction. After determining the imaging direction, the imaging method for each location on the ultrasound image can be determined. Specifically, this may include the following steps:

[0106] Step 41: Determine the imaging direction.

[0107] Step 42: Determine the imaging method corresponding to each position of the mask data on the ultrasound image based on the imaging direction.

[0108] The imaging direction can be any direction in three-dimensional space. Typically, the imaging direction is the direction in which the contact area can be observed. The imaging direction can be determined by a preset method or by the user. For example, an electronic device can recognize the user's operation, obtain the imaging direction setting information based on the recognized operation, and then determine the imaging direction.

[0109] Furthermore, in one implementation, a blank two-dimensional template can be constructed, the template being the same size as the ultrasound image, to record the imaging pattern corresponding to each location on the ultrasound image. The process of determining the imaging pattern corresponding to each location of the mask data on the ultrasound image based on the imaging direction may include:

[0110] Step 51: Construct a two-dimensional template perpendicular to the imaging direction.

[0111] Step 52: Project the mask volume data onto the two-dimensional template along the imaging direction.

[0112] Step 53: Set the identification information corresponding to the first position on the two-dimensional template to the first mode information corresponding to the first imaging mode.

[0113] Step 54: Set the identification information corresponding to the second position on the two-dimensional template to the second mode information corresponding to the second imaging mode.

[0114] Step 55: Based on the identification information of the first position and the second position in the two-dimensional template, determine the imaging mode of the ultrasound image.

[0115] Among them, the area to which the projection point corresponding to the first position belongs in the mask data is the contact area, and the position of the projection point corresponding to the second position in the mask data is the non-contact area.

[0116] It is understandable that the imaging direction is the direction in which the user observes the mask data, and the result of this observation is the ultrasound image. Depending on the specific content of the first and second imaging methods, the specific content of the ultrasound image differs, but the imaging method used at each location on the ultrasound image (i.e., whether it is the first or second imaging method) is fixed. This is because the imaging direction is fixed, and the projection of the mask data along this direction is also fixed. The projection result is the observation result, i.e., the ultrasound image, and the ultrasound image is perpendicular to the imaging direction.

[0117] Please refer to Figure 3 , Figure 3 This is a schematic diagram of a two-dimensional template setting provided in an embodiment of this application. The light rays represent the imaging direction, the three-dimensional data field represents the mask data, and the sampling points include the corresponding data points of the projection points on the mask data. In some embodiments, the projection of the mask data onto the two-dimensional template does not completely cover the entire two-dimensional template; in this case, the sampling points may also include the projection points of the projection points on invalid data. The resolution and size of the two-dimensional template are the same as the ultrasound image. Each position on it is used to record the identification information of the corresponding position in the ultrasound image, which is used to represent the imaging mode. When determining the specific state of each identification information, the mask data is projected onto the two-dimensional template along the imaging direction. It should be noted that when the mask data is projected onto the two-dimensional template, it does not utilize the values ​​of the mask data at each position on the two-dimensional template, but is used to delineate the projection range of the aforementioned contact area and non-contact area on the second template, and to set the specific states of the identification information of the first and second positions respectively. Specifically, in one embodiment, the first imaging mode can be represented by 0, and the second imaging mode can be represented by 1, or the first imaging mode can be represented by the identifier l1 of the contact surface, and the second imaging mode can be represented by the identifier l2 of the non-contact area. After all the identification information has been set, the two-dimensional template can be identified as the imaging mode information, which can be used to determine the imaging mode at various locations on the ultrasound image.

[0118] according to Figure 3 As can be seen, along the imaging direction, the projection of the mask data onto the 2D template does not completely cover the entire 2D template, meaning that invalid data may be projected onto the 2D template. In this case, once the representation information corresponding to all the first and second positions has been set, it can be determined that the identification information setting is complete.

[0119] S103: Based on the imaging method, the ultrasound image is obtained by rendering each position on the ultrasound image using mask volume data.

[0120] Once the imaging modality is determined, the ultrasound image is rendered using the mask data according to the imaging modality to obtain the corresponding ultrasound image. The specific rendering process is not limited. It is understandable that the imaging modality of an ultrasound image differs at different locations, therefore the resulting ultrasound image carries information corresponding to two different imaging modalities, resulting in a large amount of information carried by the ultrasound image.

[0121] Specifically, in one implementation, if a two-dimensional template is used to generate imaging mode information, the process of generating an ultrasound image may include:

[0122] Step 61: Based on the identification information of the first position and the second position, determine the first rendering area on the ultrasound image that corresponds to the first method information and the second rendering area that corresponds to the second method information.

[0123] Step 62: Render the first image in the first rendering area based on the first imaging method to obtain the first image.

[0124] Step 63: Render the second image in the second rendering area based on the second imaging method to obtain the second image.

[0125] Step 64: Use the first image and the second image to form an ultrasound image.

[0126] It is understandable that the identification information at different positions on the two-dimensional template corresponds to the rendering method at the corresponding position on the ultrasound image. Therefore, based on the identification information at each position on the imaging method information, a first rendering area corresponding to the first method information and a second rendering area corresponding to the second method information can be delineated on the ultrasound image. In the two rendering areas, rendering is performed based on the corresponding imaging method, and the obtained first and second images are stitched together to obtain the ultrasound image.

[0127] It should be noted that this embodiment does not limit the specific content of the first imaging method and the second imaging method. For example, in one implementation, the first imaging method may include a volume rendering method. Using a volume rendering method for imaging can add depth information of the volume data on the basis of niche imaging, so that the ultrasound image carries more information. Specifically, the process of obtaining the first image may include:

[0128] Step 71: In the first rendering area, along the imaging direction, the mask volume data is rendered using volume rendering to obtain the first image.

[0129] The volume rendering method can be any specific algorithm; this implementation uses the ray casting algorithm as an example. Please refer to... Figure 4 , Figure 4This is a schematic diagram illustrating the principle of ray projection imaging provided in this application embodiment. The basic principle of the ray projection algorithm is to emit a ray of light from each pixel on the imaging screen (i.e., the ultrasound image, whose specific location is the same as the position of the two-dimensional template) in a pre-set direction (i.e., the imaging direction), passing through the three-dimensional data field (i.e., the mask data). The ray is resampled at certain intervals, and each sampling point is obtained by trilinear interpolation of its eight nearest sampling points, and assigned a corresponding color value and opacity. Then, the sampling points on the ray are synthesized according to a synthesis formula in a front-to-back or back-to-front order. The result is the color value of the pixel position from which the ray was emitted. The user, at a viewpoint in front of the imaging screen, can see the ultrasound image based on the color value of the pixel position.

[0130] The synthesis formula is as follows:

[0131] C out α out =C in α in +C now *α now *(1.0-α in )

[0132] α out =α in +α now *(1.0-α in )

[0133] Among them, C now Let α be the color value of the i-th sampling point. now Let C be the opacity value of the i-th sampling point. in Let α be the color value of the light entering the i-th sampling point. in Let α be the opacity value when light enters the i-th sampling point. out Let C be the opacity value of light passing through the i-th sampling point. out Let i be the color value of the light passing through the i-th sampling point. i increases sequentially from zero, representing the index of the sampling point.

[0134] Furthermore, during the light projection and fusion process, the opacity of each sampling point can be adjusted using gradients to select the desired imaging effect. The opacity function is:

[0135] α now =Opa(gray)*Adj0+Grad*Adj1

[0136] Where gary is the grayscale value at the i-th sampling point, Opa is the mapping table between grayscale and opacity, Grad is the gradient value at the i-th sampling point, and Adj0 and Adj1 are preset weights. The mapping table can be preset, and the calculation process of the gradient value can be found in relevant technologies, which will not be elaborated here.

[0137] Please refer to Figure 5 , Figure 5 This is a schematic diagram of an ultrasound image provided in an embodiment of this application. The original ultrasound volume data is defined by the outermost cube-shaped frame, the ultrasound volume data itself is defined by the sphere within it, and the mask volume data is the data remaining after deleting a portion of the ultrasound volume data. The projection of the contact surface between the mask volume data and the niche volume data onto the ultrasound image is the central black-and-white alternating region. Within this region, volume rendering is used for imaging, and the resulting image is the first black-and-white alternating image.

[0138] Understandably, in volume rendering, light rays pass directly through the mask volume data along the imaging direction. Therefore, generating the first image could involve rendering the mask volume data in the first rendering area using the aforementioned ray casting rendering method to obtain the first image.

[0139] In one implementation, the light source may not completely penetrate the mask data. Instead, the last sampling point is placed within the mask data, achieving the effect of displaying data at a certain depth. By adjusting the specific position of the last sampling point within the mask data, the mask data at different light projection depths can be viewed. In this case, it can be called a ray projection rendering method based on target projection thickness. The first imaging method can be this method, and the method of generating the first image using this method can include:

[0140] Step 81: Obtain target projection thickness information.

[0141] Step 82: Based on the target projection thickness information, determine the ray stopping point corresponding to the ray projection along the imaging direction.

[0142] Step 83: In the first rendering area, the mask data is rendered based on the ray stopping point using the ray casting rendering method to obtain the first image.

[0143] Target projection thickness information refers to the distance from the imaging plane (i.e., the plane containing the ultrasound image or 2D template) to the last sampling point, i.e., the ray stopping point, in volume rendering using ray casting. Target projection thickness information can be preset or acquired in real-time when imaging is required. After obtaining the target thickness information, the position of the ray stopping point is deduced backward from the imaging plane along the imaging direction and used as the endpoint of ray casting during volume rendering. In this case, during volume rendering, the rays do not completely penetrate the mask volume data; during imaging, only a portion of the mask volume data is sampled. Therefore, the imaging result is related to this target projection thickness information. Please refer to [reference needed]. Figure 6 , Figure 6 This is another schematic diagram of an ultrasound image provided in an embodiment of this application. Figure 6 The central position is the first image obtained by using a light projection method based on the target thickness projection thickness.

[0144] Specifically, in one embodiment, the target projection thickness information includes the sampling point interval and the number of sampling points, wherein the sampling point interval is the distance between two adjacent sampling points, and the number of sampling points is the number of sampling points corresponding to each position (or pixel position) on the ultrasound image. Based on the target projection thickness information, the process of determining the light stopping point corresponding to the light projection method along the imaging direction may include:

[0145] Step 91: Obtain the final sampling point distance using the sampling point interval and the number of sampling points.

[0146] Step 92: Along the imaging direction, starting from the two-dimensional template, select a point whose distance from the starting point is equal to the distance to the final sampling point as the stopping point of the light ray.

[0147] It is understandable that the distance between the ray's stopping point and its starting point can be determined by using the sampling point interval and the number of sampling points; that is, the final sampling point distance. Using this final sampling point distance, the stopping point of the ray can be determined by working backward from the two-dimensional template where the ray's starting point is located. In another implementation, the starting point can be the first mask data encountered in the imaging direction, rather than the two-dimensional template; the specific settings can be configured as needed.

[0148] It should be noted that there are no restrictions on the specific methods for obtaining the sampling interval and the number of sampling points. For example, both parameters can be obtained through interaction with external systems, such as a user inputting the sampling interval and the number of sampling points via a mouse, keyboard, or other interactive device. Alternatively, both parameters can be obtained by reading preset values. Or, the two parameters can be obtained using either of the above methods separately. For example, the sampling interval can be preset and obtained by reading the preset value, while the number of sampling points can be obtained through interaction with external systems, such as data exchange with the user or other electronic devices.

[0149] In one implementation, the first image can be a first image obtained using a niche-shadow imaging method, which is a slice rendering method. Specifically, the process of generating the first image may include:

[0150] Step 111: Determine the first image as the projection image of the contact area of ​​the mask data onto the two-dimensional template along the imaging direction.

[0151] The facet rendering method refers to the imaging method that directly projects the contact area between the mask body data and the niche body data as the contact surface. That is, the contact surface is projected onto the two-dimensional template along the imaging direction. Since the two-dimensional template and the ultrasound image are in the same position, the projected image can be used as the first image in the first rendering area.

[0152] The specific imaging method for the second image is also not limited; for example, it can be imaged using volume rendering or surface rendering. For instance, when the second imaging method includes volume rendering, the mask volume data can be rendered using volume rendering along the imaging direction in the second rendering area to obtain the second image. Alternatively, when the second imaging method includes surface rendering, the projection image of the non-contact area of ​​the mask volume data surface onto the two-dimensional template along the imaging direction can be determined as the second image. In this embodiment, the data of the projected non-contact area only includes the non-contact area data of the mask volume data surface. During projection, only the data of these surfaces can form the projected image; the data inside the mask volume data cannot be projected to the outside.

[0153] It should be noted that the first and second imaging methods described above can be combined as needed to form different imaging modes. For example, four imaging modes can be included, represented in the form of first imaging method + second imaging method, namely volume rendering method + surface rendering method, ray projection method based on target projection thickness + surface rendering method, section rendering method + volume rendering method, and ray projection method based on target projection thickness + volume rendering method. If the imaging method information is obtained using a two-dimensional template, the first imaging method in the two-dimensional template is represented by the identifier l1 of the contact area, and the second imaging method is represented by the identifier l2 of the non-contact area. The ultrasound image is represented by dstimg, and the pixel value at coordinates (x, y) on the ultrasound image is represented by dstval. The value of the two-dimensional template maslimg at coordinates (x, y) is l. c The value of the 2D image imgV obtained by volume rendering at the coordinates (x, y) is l. v The value of the 2D image imgS obtained by face rendering methods (including cross-face rendering and surface rendering) at the coordinates (x, y) is l. s .

[0154] When using a combination of volume rendering and surface rendering, if l c =l2, then dstval = l s If l c =l1, then dstval = l v When using a combination of ray casting based on target projection thickness and surface rendering, if l c =l2, then dstval = l s If l c =l1, then dstval = l v It should be noted that at this time l v This value is calculated based on the stopping point of the light ray. Similarly, imaging can be performed in any mode.

[0155] The ultrasound imaging method provided in this application employs two different imaging modes for rendering ultrasound images. Mask volume data is obtained by removing niche volume data from ultrasound volume data. There is a contact area between the mask volume data and the niche volume data; this contact area is the cross-section displayed during niche imaging. Based on the ultrasound volume data generated after removing the niche volume data, the mask volume data can utilize the contact area to achieve niche imaging. The contact and non-contact areas on the mask volume data are projected onto different positions on the ultrasound image. To provide more information in the ultrasound image, different imaging modes are set for the contact and non-contact areas, namely a first imaging mode and a second imaging mode. Rendering is performed at each position using the corresponding imaging mode, resulting in an ultrasound image with information provided by both imaging modes. This allows the generated ultrasound image to simultaneously possess information from both imaging modes, increasing the information content of the ultrasound image.

[0156] Please refer to Figure 7 , Figure 7This is a flowchart illustrating a specific ultrasound imaging method provided in this application embodiment. The electronic device first acquires raw ultrasound volume data. The specific method of acquiring the raw ultrasound volume data is not limited; for example, it can be obtained by performing three-dimensional volume reconstruction to obtain three-dimensional ultrasound volume data. Mask volume data, i.e., ultrasound volume data, is generated without removing niche data. Specifically, invalid data in the raw ultrasound volume data can be set to 0 to remove invalid data and obtain the ultrasound volume data. Marking the mask volume data involves removing niche data from the ultrasound volume data to obtain the mask volume data, and simultaneously marking the contact areas of the mask volume data. The imaging mode is determined using a two-dimensional template, i.e., the imaging direction is determined, and the projection of the mask volume data is received using the two-dimensional template. Then, based on the position (contact area or non-contact area) of the projection point in the mask volume data, the specific content of the identification information at each position on the two-dimensional template is set. Based on the specific content of the identification information and the current operating mode of the electronic device, the specific content of each imaging mode can be determined, such as determining the rendering mode and color mode corresponding to each position on the ultrasound image. After determining the specific content of the imaging mode, the ultrasound image is rendered using the mask volume data based on the imaging mode to obtain the ultrasound image.

[0157] The ultrasonic imaging device provided in the embodiments of this application is described below. The ultrasonic imaging device described below can be referred to in correspondence with the ultrasonic imaging method described above.

[0158] Please refer to Figure 8 , Figure 8 A schematic diagram of an ultrasound imaging device provided in this application embodiment includes:

[0159] The mask volume acquisition module 110 is used to obtain mask volume data based on ultrasound volume data after removing niche shadow volume data; wherein, the niche shadow volume data is the volume data corresponding to the niche shadow region in the ultrasound image;

[0160] The mode determination module 120 is used to determine the imaging mode corresponding to each position of the mask data on the ultrasound image; wherein, the first imaging mode corresponding to the contact area between the mask data and the niche data is different from the second imaging mode corresponding to the non-contact area in the mask data.

[0161] The generation module 130 is used to render various positions on the ultrasound image using mask volume data according to the imaging method to obtain the ultrasound image.

[0162] Optionally, the mask body acquisition module 110 includes:

[0163] The ultrasound body acquisition unit is used to acquire ultrasound body data corresponding to ultrasound images;

[0164] The niche removal unit is used to acquire niche information corresponding to the niche region in the ultrasound image, and to separate and delete the niche data corresponding to the niche information from the ultrasound data.

[0165] The mask body determination unit is used to determine the ultrasonic body data that has been separated and the niche shadow body data deleted as mask body data.

[0166] Optionally, the ultrasound body acquisition unit includes:

[0167] The raw acquisition subunit is used to acquire raw ultrasound body data;

[0168] The effective determination unit is used to acquire effective data range information and determine the effective data corresponding to the effective data range information in the original ultrasound body data;

[0169] The ultrasound body determination subunit is used to obtain ultrasound body data based on valid data in the original ultrasound body data.

[0170] Optionally, the niche information includes niche coordinates and quadrant specification information;

[0171] The niche image deletion unit includes:

[0172] The planar construction sub-unit is used to construct three planes; the three planes are perpendicular to each other in pairs, and the coordinates of the intersection of the three planes are the coordinates of the niche shadow body;

[0173] The segmentation sub-unit is used to segment the ultrasound body data according to the plane to obtain multiple ultrasound body quadrant data;

[0174] The delete sub-unit is used to identify the target ultrasound body quadrant data corresponding to the quadrant specified information as niche shadow body data and delete it.

[0175] Optionally, the method determination module 120 includes:

[0176] Orientation determination unit, used to determine the imaging orientation;

[0177] The mode determination unit is used to determine the imaging mode corresponding to each position of the mask data on the ultrasound image based on the imaging direction.

[0178] Optionally, the method determining unit includes:

[0179] Two-dimensional template construction subunit, used to construct a two-dimensional template perpendicular to the imaging direction;

[0180] The projection subunit is used to project the mask volume data onto the two-dimensional template along the imaging direction;

[0181] The first setting subunit is used to set the identification information corresponding to the first position on the two-dimensional template as the first mode information corresponding to the first imaging mode; wherein, the area to which the projection point corresponding to the first position belongs on the mask data is the contact area;

[0182] The second setting unit is used to set the identification information corresponding to the second position on the two-dimensional template to the second mode information corresponding to the second imaging mode; wherein, the area to which the projection point corresponding to the second position belongs on the mask data is a non-contact area.

[0183] The imaging mode determination subunit is used to determine the imaging mode of the ultrasound image based on the identification information of the first and second positions in the two-dimensional template.

[0184] Optionally, the generation module 130 includes:

[0185] The region division unit is used to determine, based on the identification information of the first position and the second position, the first rendering region on the ultrasound image corresponding to the first method information and the second rendering region corresponding to the second method information.

[0186] The first rendering unit is used to render a first image in a first rendering area based on a first imaging method.

[0187] The second rendering unit is used to render a second image in the second rendering area based on the second imaging method.

[0188] A combination unit is used to compose an ultrasound image using a first image and a second image.

[0189] Optionally, the first imaging method includes volume rendering;

[0190] The first rendering unit includes:

[0191] The first volume rendering subunit is used to render the mask volume data in the first rendering area along the imaging direction using volume rendering to obtain the first image.

[0192] Optionally, the first imaging method includes a ray-casting rendering method based on the target projection thickness;

[0193] The first rendering unit includes:

[0194] The thickness information acquisition subunit is used to acquire the target projection thickness information;

[0195] The stop point determination subunit is used to determine the stop point of the light beam along the imaging direction based on the target projection thickness information;

[0196] The ray casting rendering subunit is used to render the mask volume data based on the ray stopping point in the first rendering area using the ray casting rendering method to obtain the first image.

[0197] Optionally, the target projection thickness information includes the sampling point interval and the number of sampling points;

[0198] The thickness information acquisition subunit includes:

[0199] The distance calculation subunit is used to obtain the final sampling point distance using the sampling point interval and the number of sampling points;

[0200] The positioning subunit is used to select a point along the imaging direction, starting from the two-dimensional template, and with the distance from the starting point equal to the distance to the final sampling point, as the stopping point of the light ray.

[0201] Optionally, the first imaging method includes a faceted rendering method;

[0202] The first rendering unit includes:

[0203] The section rendering subunit is used to determine the first image as the projection image of the contact area of ​​the mask volume data onto the two-dimensional template along the imaging direction.

[0204] Optionally, the second imaging method includes volume rendering;

[0205] The second rendering unit includes:

[0206] The second volume rendering subunit is used to render the mask volume data in the second rendering area along the imaging direction using volume rendering to obtain the second image.

[0207] Optionally, the second imaging method includes a surface rendering method;

[0208] The second rendering unit includes:

[0209] The surface rendering subunit is used to determine the projection image of the non-contact area of ​​the mask volume data onto the two-dimensional template along the imaging direction as a second image.

[0210] The ultrasonic device provided in the embodiments of this application is described below. The ultrasonic device described below and the ultrasonic imaging method described above can be referred to each other.

[0211] Please refer to Figure 9 , Figure 9 This is a schematic diagram of the structure of an ultrasonic device provided in an embodiment of this application. The ultrasonic device 100 may include a processor 101 and a memory 102, and may further include one or more of the following: a multimedia component 103, an information input / output (I / O) interface 104, and a communication component 105.

[0212] The processor 101 controls the overall operation of the ultrasound device 100 to complete all or part of the steps in the ultrasound imaging method described above. The memory 102 stores various types of data to support the operation of the ultrasound device 100. This data may include, for example, instructions for any application or method operating on the ultrasound device 100, as well as application-related data. The memory 102 can be implemented by any type of volatile or non-volatile storage device or a combination thereof, such as one or more of Static Random Access Memory (SRAM), Electrically Erasable Programmable Read-Only Memory (EEPROM), Erasable Programmable Read-Only Memory (EPROM), Programmable Read-Only Memory (PROM), Read-Only Memory (ROM), magnetic storage, flash memory, magnetic disk, or optical disk.

[0213] Multimedia component 103 may include a screen and an audio component. The screen may be, for example, a touchscreen, and the audio component is used to output and / or input audio signals. For example, the audio component may include a microphone for receiving external audio signals. The received audio signals may be further stored in memory 102 or transmitted via communication component 105. The audio component also includes at least one speaker for outputting audio signals. I / O interface 104 provides an interface between processor 101 and other interface modules, such as a keyboard, mouse, buttons, etc. These buttons may be virtual or physical buttons. Communication component 105 is used for wired or wireless communication between ultrasound device 100 and other devices. Wireless communication may include Wi-Fi, Bluetooth, Near Field Communication (NFC), 2G, 3G, or 4G, or a combination of these. Therefore, the corresponding communication component 105 may include a Wi-Fi component, a Bluetooth component, and an NFC component.

[0214] The ultrasound device 100 may be implemented by one or more application-specific integrated circuits (ASICs), digital signal processors (DSPs), digital signal processing devices (DSPDs), programmable logic devices (PLDs), field-programmable gate arrays (FPGAs), controllers, microcontrollers, microprocessors, or other electronic components to perform the ultrasound imaging method given in the above embodiments.

[0215] The following describes the computer-readable storage medium provided in the embodiments of this application. The computer-readable storage medium described below can be referred to in correspondence with the ultrasound imaging method described above.

[0216] This application also provides a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the steps of the ultrasound imaging method described above.

[0217] The computer-readable storage medium may include various media capable of storing program code, such as USB flash drives, portable hard drives, read-only memory (ROM), random access memory (RAM), magnetic disks, or optical disks.

[0218] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on its differences from other embodiments. Similar or identical parts between embodiments can be referred to interchangeably. For the apparatus disclosed in the embodiments, since it corresponds to the method disclosed in the embodiments, the description is relatively simple; relevant parts can be referred to in the method section.

[0219] Those skilled in the art will further recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, computer software, or a combination of both. To clearly illustrate the interchangeability of hardware and software, the components and steps of the various examples have been generally described in terms of functionality in the foregoing description. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0220] The steps of the methods or algorithms described in conjunction with the embodiments disclosed herein can be implemented directly by hardware, a software module executed by a processor, or a combination of both. The software module can be located in random access memory (RAM), main memory, read-only memory (ROM), electrically programmable ROM, electrically erasable programmable ROM, registers, hard disk, removable disk, CD-ROM, or any other form of storage medium known in the art.

[0221] Finally, it should be noted that in this document, relationships such as "first" and "second" are used merely to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "include," "contain," or any other variations are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus.

[0222] This document uses specific examples to illustrate the principles and implementation methods of this application. The descriptions of the above embodiments are only for the purpose of helping to understand the methods and core ideas of this application. At the same time, for those skilled in the art, there will be changes in the specific implementation methods and application scope based on the ideas of this application. Therefore, the content of this specification should not be construed as a limitation of this application.

Claims

1. An ultrasound imaging method, characterized in that, include: Mask volume data is obtained from ultrasound volume data after removing niche shadow volume data; wherein, the niche shadow volume data is the volume data corresponding to the niche shadow region in the ultrasound image; The imaging mode corresponding to each position of the mask data on the ultrasound image is determined; wherein, the first imaging mode corresponding to the contact area between the mask data and the niche data is different from the second imaging mode corresponding to the non-contact area in the mask data. According to the imaging method, the ultrasound image is obtained by rendering the various positions on the ultrasound image using the mask data. The ultrasonic body data obtained based on the removed niche shadow body data to obtain mask body data includes: Obtain niche body information corresponding to the niche region in the ultrasound image, and separate and delete the niche body data corresponding to the niche body information from the ultrasound body data; The step of determining the imaging method corresponding to each position of the mask data on the ultrasound image includes: Determine the imaging direction; Based on the imaging direction, determine the imaging method corresponding to each position of the mask data on the ultrasound image; The step of determining the imaging method corresponding to each position of the mask data on the ultrasound image based on the imaging direction includes: Construct a two-dimensional template perpendicular to the imaging direction; Along the imaging direction, the mask data is projected onto the two-dimensional template; The identification information corresponding to the first position on the two-dimensional template is set as the first mode information corresponding to the first imaging mode; wherein, the area to which the projection point corresponding to the first position belongs on the mask data is the contact area; The identification information corresponding to the second position on the two-dimensional template is set as the second mode information corresponding to the second imaging mode; wherein, the area to which the projection point corresponding to the second position belongs on the mask data is the non-contact area; Based on the identification information of the first and second positions in the two-dimensional template, the imaging mode of the ultrasound image is determined.

2. The ultrasound imaging method according to claim 1, characterized in that, The ultrasonic body data obtained based on the removed niche shadow body data to obtain mask body data includes: Acquire ultrasound body data corresponding to ultrasound images; The ultrasonic body data from which the niche shadow data is separated and deleted is determined as the mask body data.

3. The ultrasound imaging method according to claim 2, characterized in that, The acquisition of ultrasound body data corresponding to the ultrasound image includes: Obtain raw ultrasound body data; Obtain valid data range information, and determine the valid data corresponding to the valid data range information in the original ultrasound body data; The ultrasound body data is obtained based on the valid data in the original ultrasound body data.

4. The ultrasound imaging method according to claim 2, characterized in that, The niche shadow body information includes niche shadow body coordinates and quadrant specification information; The process of separating and deleting the niche data corresponding to the niche information from the ultrasound body data includes: Construct three planes; the three planes are perpendicular to each other in every pair, and the coordinates of the intersection of the three planes are the coordinates of the niche shadow body; The ultrasound body data is segmented according to the plane to obtain multiple ultrasound body quadrant data; The target ultrasound body quadrant data corresponding to the quadrant specified information is determined as the niche shadow body data and deleted.

5. The ultrasound imaging method according to claim 1, characterized in that, The step of rendering the ultrasound image at various locations using the mask data according to the imaging method to obtain the ultrasound image includes: Based on the identification information of the first position and the second position, a first rendering area corresponding to the first method information and a second rendering area corresponding to the second method information on the ultrasound image are determined; A first image is obtained by rendering the first image in the first rendering area based on the first imaging method; A second image is obtained by rendering in the second rendering area based on the second imaging method; The ultrasound image is composed of the first image and the second image.

6. The ultrasound imaging method according to claim 5, characterized in that, The first imaging method includes a volume rendering method; the step of rendering the first image in the first rendering area based on the first imaging method to obtain a first image includes: In the first rendering area, along the imaging direction, the mask volume data is rendered using the volume rendering method to obtain the first image; and / or The second imaging method includes a volume rendering method; the step of rendering the second image in the second rendering area based on the second imaging method to obtain a second image includes: In the second rendering area, along the imaging direction, the mask volume data is rendered using the volume rendering method to obtain the second image.

7. The ultrasound imaging method according to claim 5, characterized in that, The first imaging method includes a ray projection rendering method based on the target projection thickness; The step of rendering the first image in the first rendering area based on the first imaging method to obtain the first image includes: Obtain target projection thickness information; Based on the target projection thickness information, determine the light stopping point corresponding to the light projection along the imaging direction; In the first rendering area, the mask data is rendered based on the light stopping point using the light projection rendering method to obtain the first image.

8. The ultrasound imaging method according to claim 7, characterized in that, The target projection thickness information includes the sampling point interval and the number of sampling points; The step of determining the ray stopping point corresponding to the ray projection along the imaging direction based on the target projection thickness information includes: The final sampling point distance is obtained using the sampling point interval and the number of sampling points; Along the imaging direction, starting from the two-dimensional template, a point whose distance from the starting point is equal to the distance from the final sampling point is selected as the light stopping point.

9. The ultrasound imaging method according to claim 5, characterized in that, The first imaging method includes a slice rendering method; The step of rendering the first image in the first rendering area based on the first imaging method to obtain the first image includes: The projection image of the contact area of ​​the mask data onto the two-dimensional template along the imaging direction is determined as the first image.

10. The ultrasound imaging method according to claim 5, characterized in that, The second imaging method includes surface rendering; The step of rendering the second image in the second rendering area based on the second imaging method to obtain the second image includes: The projection image of the non-contact area of ​​the mask data onto the two-dimensional template along the imaging direction is determined as the second image.

11. An ultrasonic imaging device, characterized in that, include: The mask volume acquisition module is used to obtain mask volume data based on ultrasound volume data after removing niche shadow volume data; wherein, the niche shadow volume data is the volume data corresponding to the niche shadow region in the ultrasound image; The mode determination module is used to determine the imaging mode corresponding to each position of the mask data on the ultrasound image; wherein, the first imaging mode corresponding to the contact area between the mask data and the niche data is different from the second imaging mode corresponding to the non-contact area in the mask data. A generation module is used to render the ultrasound image at each position using the mask data according to the imaging method to obtain the ultrasound image; The mask acquisition module includes: The niche removal unit is used to acquire niche information corresponding to the niche region in the ultrasound image, and to separate and delete the niche data corresponding to the niche information from the ultrasound data. The method determination module includes: Orientation determination unit, used to determine the imaging orientation; The mode determination unit is used to determine the imaging mode corresponding to each position of the mask data on the ultrasound image based on the imaging direction. The method determination unit includes: A two-dimensional template construction subunit is used to construct a two-dimensional template perpendicular to the imaging direction; A projection subunit is used to project the mask data onto the two-dimensional template along the imaging direction; The first setting subunit is used to set the identification information corresponding to the first position on the two-dimensional template as the first mode information corresponding to the first imaging mode; wherein, the area to which the projection point corresponding to the first position belongs on the mask data is the contact area; The second setting subunit is used to set the identification information corresponding to the second position on the two-dimensional template as the second mode information corresponding to the second imaging mode; wherein, the area to which the projection point corresponding to the second position belongs on the mask data is the non-contact area; An imaging mode determination subunit is used to determine the imaging mode of the ultrasound image based on the identification information of the first position and the second position in the two-dimensional template.

12. An ultrasonic device, characterized in that, Includes memory and processor, wherein: The memory is used to store computer programs; The processor is configured to execute the computer program to implement the ultrasound imaging method as described in any one of claims 1 to 10.

13. A computer-readable storage medium, characterized in that, Used to store a computer program, wherein the computer program, when executed by a processor, implements the ultrasound imaging method as described in any one of claims 1 to 10.

Images