Ultrasound imaging method, system and computer readable storage medium

Abstract

An ultrasonic imaging method, system and computer readable storage medium. The method comprises: controlling a full volume probe in a first imaging mode to emit a first ultrasonic wave at a first preset position to obtain three-dimensional volume data of a measured tissue (200); determining a region of interest of the measured tissue based on the three-dimensional volume data (202); controlling the full volume probe in a second imaging mode to emit a second ultrasonic wave at a second preset position to the region of interest of the measured tissue (204); and determining physiological state information of the region of interest of the measured tissue based on the second ultrasonic wave (206). The method can apply a full volume imaging system of non-planar tissue to other imaging modes to detect physiological state information of the measured tissue, and can also increase the application range of the full volume imaging system of non-planar tissue.

Description

Technical Field

[0001] The present application relates to the medical field, and in particular to an ultrasound imaging method, system, and computer-readable storage medium. Background Art

[0002] During full-volume imaging, because the structure of tissues like the breast is non-planar, and full-volume imaging must be coupled to the tissue, the probe is often tightly squeezed to the point of deformation during imaging to capture full-volume information. However, this compression alters the elasticity of the tissue, and the blood supply within the tissue may become abnormal. Consequently, when acquiring volumetric information of non-planar tissue, the system cannot capture physiological information about the tissue, such as blood flow and elasticity, that can be extracted using other imaging modes. Summary of the Invention

[0003] The present application provides an ultrasound imaging method, system, and computer-readable storage medium.

[0004] A first aspect of an embodiment of the present application provides an ultrasound imaging method, which is applied to an ultrasound imaging system, wherein the ultrasound imaging system includes an ultrasound probe. The ultrasound imaging method includes:

[0005] Controlling the ultrasonic probe in the first imaging mode to transmit a first ultrasonic wave to the measured tissue at a first preset position, and converting the first ultrasonic echo returned by the measured tissue to obtain first ultrasonic echo data;

[0006] acquiring three-dimensional volume data of the measured tissue based on the first ultrasonic echo data;

[0007] determining a region of interest of the measured tissue based on the three-dimensional volume data;

[0008] Controlling the ultrasound probe to move from the first preset position to a second preset position, wherein a first distance of the first preset position relative to a reference position of the measured tissue is smaller than a second distance of the second preset position relative to the reference position of the measured tissue;

[0009] Controlling the ultrasonic probe in the second imaging mode to transmit a second ultrasonic wave to the region of interest of the measured tissue, and converting the second ultrasonic echo returned by the measured tissue to obtain second ultrasonic echo data;

[0010] Physiological state information of the region of interest is determined based on the second ultrasound echo data.

[0011] A second aspect of the application embodiment provides an ultrasound imaging method, which is applied to an ultrasound imaging system, wherein the ultrasound imaging system includes an ultrasound probe, and the ultrasound imaging method includes:

[0012] Acquiring three-dimensional volume data of the measured tissue collected by the ultrasound probe in the first imaging mode at a first preset position;

[0013] determining a region of interest of the measured tissue based on the three-dimensional volume data of the measured tissue;

[0014] Controlling the ultrasound probe to move from a first preset position to a second preset position, wherein a first distance of the first preset position relative to a reference position of the measured tissue is smaller than a second distance of the second preset position relative to the reference position of the measured tissue;

[0015] controlling the ultrasound probe in the second imaging mode to transmit ultrasound waves to the region of interest of the measured tissue at the second preset position, and converting ultrasound echoes returned by the measured tissue to obtain ultrasound echo data;

[0016] Physiological state information of the region of interest is determined based on the ultrasound echo data.

[0017] A third aspect of the application embodiment provides an ultrasound imaging system, comprising:

[0018] Full volume probe, selectively working in the first imaging mode or the second imaging mode;

[0019] A processor is connected to the full-volume probe, and is used to control the full-volume probe in the first imaging mode to transmit a first ultrasonic wave to the measured tissue, and convert the first ultrasonic echo returned by the measured tissue to obtain first ultrasonic echo data; the processor obtains three-dimensional volume data of the measured tissue based on the first ultrasonic echo data, and determines the region of interest of the measured tissue based on the three-dimensional volume data; the processor is used to control the full-volume probe in the second imaging mode to transmit a second ultrasonic wave to the region of interest of the measured tissue, and convert the second ultrasonic echo returned by the measured tissue to obtain second ultrasonic echo data; the processor also determines physiological status information of the region of interest based on the second ultrasonic echo data.

[0020] A fourth aspect of an embodiment of the present application provides a computer-readable storage medium, which is used to store a computer program for electronic data exchange, wherein the computer program enables a computer to execute some or all of the steps described in any method of the first aspect of an embodiment of the present application.

[0021] Embodiments of the present application provide an ultrasound imaging method, system, and computer-readable storage medium for acquiring a region of interest in three-dimensional volumetric data of a tested tissue at a first preset position in a first imaging mode, and acquiring physiological state information of the region of interest of the tested tissue at a second preset position in a second imaging mode. This allows the full-volume imaging system for non-planar tissue to be applied to other imaging modes to detect physiological state information of the tested tissue, thereby expanding the application scope of the full-volume imaging system for non-planar tissue. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] In order to more clearly illustrate the implementation methods of the present application or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the implementation methods or the description of the prior art. Obviously, the drawings described below are only some implementation methods of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative labor.

[0023] Figure 1 Schematic diagram of the system structure of an ultrasound imaging system in one embodiment of the present application.

[0024] Figure 2 This is a flowchart of the steps of the ultrasound imaging method in one embodiment of the present application.

[0025] Figure 3 Schematic diagram of the state of the tested tissue under different imaging modes in one embodiment of the present application.

[0026] Figure 4 Schematic diagram of the structure of a probe according to an embodiment of the present application.

[0027] Figure 5 FIG. 1 is a schematic diagram of an arrangement of array elements of a first type of transducer in an embodiment of the present application.

[0028] Figure 6 FIG. 1 is a schematic diagram of an array element arrangement of a second type of transducer in an embodiment of the present application.

[0029] Figure 7 Schematic diagram of a region of interest in one embodiment of the present application.

[0030] Figure 8 Schematic diagram of a region of interest in another embodiment of the present application.

[0031] Figure 9 It is a block diagram of an ultrasound imaging system according to another embodiment of the present application.

[0032] Figure 10 Schematic diagram of the structure of an ultrasonic breast machine in one embodiment of the present application. DETAILED DESCRIPTION

[0033] In order to enable those skilled in the art to better understand the present invention, the technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the accompanying drawings in the embodiments of the present invention. The described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments in the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0034] The terms "first," "second," and the like in the specification and claims of this application and the accompanying drawings are used to distinguish between different objects, not to describe a particular order. Furthermore, the terms "including," "having," and any variations thereof, are intended to cover non-exclusive inclusions. For example, a process, method, system, product, or apparatus comprising a series of steps or elements is not limited to the listed steps or elements but may optionally include steps or elements not listed, or may optionally include other steps or elements inherent to the process, method, product, or apparatus.

[0035] References to "embodiments" herein mean that the features, structures, or characteristics described in connection with the embodiments may be included in at least one embodiment of the present application. The appearance of this phrase in various places in the specification does not necessarily refer to the same embodiment, nor does it constitute an independent or alternative embodiment that is mutually exclusive of other embodiments. It is understood, both explicitly and implicitly, by those skilled in the art that the embodiments described herein may be combined with other embodiments.

[0036] It should be noted that, for the sake of simplicity of description, the following method embodiments are all expressed as a series of action combinations. However, those skilled in the art should know that this application is not limited to the order of the actions described, because according to this application, certain steps can be performed in other orders or simultaneously.

[0037] See also Figure 1 , which is a schematic diagram of the system structure of an ultrasound imaging system according to one embodiment of the present application. The ultrasound imaging system 10 may include an ultrasound probe 100, a transmitting circuit 102 connected to the ultrasound probe 100, a receiving circuit 104 connected to the ultrasound probe 100, a beamforming module 106, a signal processing module 108, an imaging processing module 110, and a display 112. The receiving circuit 104, the beamforming module 106, the signal processing module 108, the imaging processing module 110, and the display 112 may be electrically connected in sequence.

[0038] In this embodiment, the ultrasound imaging system 10 may be an imaging system that supports automatic breast volume imaging (ABVS) of the breast. Figure 10An ultrasonic breast machine is shown, which includes: a body 11, a cantilever 9, casters 10 and a probe box 8. The probe box 8 is provided with a movable ultrasonic probe. The upper end of the probe box 8 is mounted on the cantilever 9 via a rotating device, and is movably mounted on the body 11 via the cantilever 9. The lower end of the body 11 is mounted with casters 10. The installation of the casters 10 facilitates the movement of the entire breast machine. The ultrasonic probe of the breast machine is movable or swingable, thereby achieving full-volume imaging of the breast. Correspondingly, in conjunction with the automatic full-volume breast imaging mode of the breast machine, the ultrasonic probe of the breast machine is generally referred to as a full-volume probe in the industry.

[0039] The ultrasound imaging system of this embodiment, such as an ultrasound breast machine, can obtain the image of the tested tissue 40 (shown in FIG. Figure 3 ) and then detecting part of the tested tissue contained in the region of interest in the second imaging mode to obtain physiological status information of the region of interest.

[0040] Please also refer to Figure 2 , shown is a flowchart of the steps of an ultrasound imaging method in one embodiment of the present application. The ultrasound imaging method includes the following steps:

[0041] Step 200 : Controlling an ultrasound probe in a first imaging mode to transmit a first ultrasound wave at a first preset position to obtain three-dimensional volume data of a tissue under test.

[0042] In this embodiment, the first imaging mode can be a full volume imaging mode. Figure 3 ) is a non-planar structure. For example, the tissue 40 to be tested may be a human breast. Therefore, when obtaining the three-dimensional volume data 490 (shown in FIG. 1 ), Figure 7 ), the probe 100 needs to press the tissue under test 40 so that the morphology of the tissue under test 40 remains unchanged during the acquisition process.

[0043] Please also refer to Figure 3 , which shows a schematic diagram of the state of the measured tissue under different imaging modes in one embodiment of the present application. It includes a horizontal axis and a vertical axis. The vertical axis represents the preset positions of the probe 100, each of which represents the distance information of the probe 100 relative to the reference position of the measured tissue 40. The horizontal axis represents the time during the detection process.

[0044] For example, in the first imaging mode, at a first preset time T1, the probe 100 can move to a first preset position V1 to compress and secure the non-planar tissue under test 40. At this point, the tissue under test 40 is in a compressed state, and the transmitting circuit 102 transmits a first ultrasonic wave to the tissue under test 40 through the probe 100. After a certain delay, the probe 100 receives a first ultrasonic echo containing information about the object being tested, which is reflected from the tissue under test 40. The probe 100 converts this first ultrasonic echo into an electrical signal. The receiving circuit 104 receives the electrical signal converted by the probe 100, obtains first ultrasonic echo data, and transmits this first ultrasonic echo data to the beamforming module 106. The beamforming module 106 performs beamforming processing on the first ultrasonic echo data, including focusing delay, weighting, and channel summing. The processed first ultrasonic echo data is then transmitted to the signal processing module 108 for related signal processing. The first ultrasound echo data processed by the signal processing module 108 is sent to the imaging processing module 110. The imaging processing module 110 processes the first ultrasound echo data differently based on the imaging mode desired by the user to obtain tissue image data in different modes. The data is then processed through logarithmic compression, dynamic range adjustment, digital scan conversion, and other processes to form ultrasound tissue images in different modes, which are then displayed on the display 112. The ultrasound tissue images in different modes may include two-dimensional images such as B-images, or three-dimensional images. In this embodiment, non-planar tissue refers to tissue that needs to be fixed or compressed when acquiring volumetric data of the tissue.

[0045] Please also refer to Figure 4 , which is a schematic diagram of the structure of a probe according to an embodiment of the present application. The probe 100 may include a support assembly 120, a pressing plate 140 disposed on one end surface of the support assembly 120, and a transducer 130 disposed within the support assembly 120. The support assembly 120 is generally a rectangular parallelepiped structure, with rails 122 disposed on two opposite sides. The transducer 130 is disposed on the rails 122 of the support assembly 120 and can be driven by a driving mechanism 806 (shown in FIG. Figure 8 ) is driven by the drive mechanism 806 to move in the longitudinal direction of the track 122 (e.g., along the positive or negative direction of the X-axis). For example, at a first time T1, when the probe 100 presses the tissue under test 40 to the first preset position V1, the pressing plate 140 of the probe 100 contacts and presses the tissue under test 40. At this time, the tissue under test 40 is in a compressed state, and the drive mechanism 806 controls the transducer 130 to move in the longitudinal direction of the track 122 to acquire three-dimensional volume data 490 of the tissue under test 40.

[0046] Please also refer to Figure 5, which is a schematic diagram of the array element arrangement of the first type transducer in one embodiment of the present application. In this embodiment, the probe 100 includes a first type transducer, wherein the first type transducer has array elements 132 arranged in a linear array (e.g., the transducer 130 includes array elements 132 arranged in a row). When the ultrasound imaging system 10 acquires three-dimensional volumetric data of the measured tissue 30 using the first type transducer, because the probe 100 is pressed against the measured tissue 40 as a whole and remains stationary, the transducer 130 can be driven by the drive mechanism 806 to move at a specific speed along the length direction of the track 122 to scan the entire probe area, wherein the measured tissue 40 is located within the probe area.

[0047] In one embodiment, when the transducer 130 moves along the positive direction of the X-axis to acquire full-volume data of the tissue under test 40, the transducer 130 may move from a first position to a second position to complete full-volume imaging of the tissue under test 40. After the full-volume scan is completed, the transducer 130 may be located at the scan end position (e.g., the second position) or may return to the initial position set by the system (e.g., the first position). Since the transducer 130, which has linear array elements, moves along the length of the track 122, the imaging processing module 110 may acquire a plurality of frames of two-dimensional B images corresponding to various positions of the tissue under test 40 along the length of the track 122. After performing a three-dimensional reconstruction operation on the plurality of two-dimensional B images, the imaging processing module 110 generates a three-dimensional image in a stereoscopic space, thereby obtaining three-dimensional volume data 490 corresponding to the tissue under test 40, wherein the three-dimensional volume data 490 includes a plurality of volume data. In this way, the imaging processing module 110 can match each frame of image with a spatial position according to the order in which each frame of image is acquired and the speed at which the probe 100 moves. Thus, each volume of data in the three-dimensional volume data 490 also has a corresponding coordinate system (as shown in FIG. Figure 7 The three-dimensional space coordinate value in the oXYZ three-dimensional coordinate system).

[0048] Please also refer to Figure 6, which is a schematic diagram illustrating the arrangement of array elements of a second-type transducer in one embodiment of the present application. In this embodiment, the probe 100 includes a second-type transducer having array elements 132 arranged in a matrix (e.g., the transducer 130 includes array elements 132 arranged in a planar array with multiple rows and columns). When the ultrasound imaging system 10 acquires three-dimensional volumetric data of the tissue under examination 40 using the second-type transducer, the probe 100 can control the excitation delay of each array element 132 in the transducer 130 to generate a first ultrasonic wave, and can also move the position of the transducer 130 along the length of the track 122 to acquire three-dimensional volumetric data of the tissue under examination 40. As the transducer 130, having the array elements arranged in a matrix, moves along the length of the track 122, the imaging processing module 110 can acquire multiple frames of two-dimensional B-images or three-dimensional images of the tissue under examination 40 corresponding to various positions along the length of the track 122. The two-dimensional B-images can be acquired when some of the array elements in the second-type transducer emit the first ultrasonic wave. Therefore, the imaging processing module 110 can generate a three-dimensional image of a three-dimensional space after three-dimensional reconstruction of several frames of two-dimensional B images, or synthesize the three-dimensional images corresponding to each position to obtain three-dimensional volume data 490 of the measured tissue 40, wherein the three-dimensional volume data 490 also includes a plurality of volume data. Therefore, the imaging processing module 110 can correspond each frame of image to a spatial position one by one according to the order in which each frame of image is acquired and the speed at which the probe 100 moves, that is, each volume data in the three-dimensional volume data has a corresponding coordinate system (as shown in FIG. Figure 7 In one embodiment, by controlling the excitation delay of each element 132 in the transducer 130, first ultrasonic waves with different deflection angles can be generated. Therefore, if the first ultrasonic waves with different deflection angles generated by the second-type transducer can cover the entire space where the examined tissue 40 is located or a portion (non-section) of the space where the examined tissue 40 is located, the second-type transducer does not need to move on the track 122 or can move within a portion of the track 122 when acquiring volumetric data of the examined tissue 40.

[0049] Step 202: determining a region of interest of the measured tissue based on the three-dimensional volume data.

[0050] In one embodiment, the region of interest of the tissue under test 40 may be determined manually by a user or automatically.

[0051] Please also refer to Figure 7, shown is a schematic diagram of the region of interest in one embodiment of the present application. In manual mode, the imaging processing module 110 can receive the user's input operation through the input interface, and determine the region of interest of the measured tissue 40 based on the input operation. For example, the imaging processing module 110 can control the first section image 400 corresponding to the preset position in the three-dimensional volume data 490 to be displayed on the display 112. When the user determines that the first section image 400 contains a lesion of interest, the user can mark it in the first section image 400, such as drawing a selection area 410 with a mouse. In this way, the imaging processing module 110 can receive the user's input operation of drawing the region of interest with a mouse. Furthermore, the imaging processing module 110 determines that the volume data contained in the selection area 410 is the region of interest. In other embodiments, the user can also select a selection area containing any position in the first section image 400 as the region of interest.

[0052] Please also refer to Figure 8 , shown is a schematic diagram of a region of interest in another embodiment of the present application. In an automatic mode, the imaging processing module 110 can determine a target region containing a lesion in the three-dimensional volume data 490 based on the processing model, and determine that the target region is the region of interest. The imaging processing module 110 can control the slicing operation on the three-dimensional volume data 490 to obtain a first preset number of slice images, and determine a second preset number of slice images of the target region containing the lesion in the first preset number based on the processing model, wherein the second preset number of slice images have corresponding priorities. For example, the imaging processing module 110 can perform a slice operation on the three-dimensional volume data 490 parallel to the XZ plane to obtain a second slice image 402, a third slice image 404, and a fourth slice image 406.

[0053] The imaging processing module 110 may further select, according to a preset rule, a target region included in a slice image with the highest priority among the second preset number as the region of interest.

[0054] In an embodiment, the imaging processing module 110 can determine the second preset number of cross-sectional images containing the target region of the lesion in the first preset number based on an image segmentation model, or the imaging processing module 110 can determine the second preset number of cross-sectional images containing the target region of the lesion in the first preset number based on a learning model. The image segmentation model can include one or more of a parametric active contour model (Snake), a graph cut model, a level set model, and a random walker model, and the learning model can include one or more of a KNN (k-Nearest Neighbor) algorithm, a SVM (Support Vector Machine), a random forest, and a neural network. For specific processing models, refer to related technologies.

[0055] In the embodiment, the imaging processing module 110 determines that the target region 412 in the second cross-sectional image 402 contains the lesion, the target region 414 in the third cross-sectional image 404 contains the lesion, and the fourth cross-sectional image 406 does not contain the lesion. Therefore, the second preset number of cross-sectional images contains the second cross-sectional image 402 and the third cross-sectional image 404. Since each of the second preset number of cross-sectional images contains the target region of the lesion, the imaging processing module 110 can determine the priority of each of the second preset number of cross-sectional images according to a preset rule such as the size of the target region of the lesion contained in each of the second preset number of cross-sectional images, the clarity of the target region of the lesion contained in each of the second preset number of cross-sectional images, or a preset rule such as the area of the target region of the lesion and the corresponding first weight, the clarity of the target region of the lesion and the corresponding second weight, and the like. For example, the imaging processing module 110 can determine that the priority of the cross-sectional image containing the target region of the lesion with the largest area is the highest, or the priority of the cross-sectional image containing the target region of the lesion with the highest clarity is the highest, or the priority of the cross-sectional image containing the target region of the lesion with the largest area S1 and the corresponding first weight W1 and the cross-sectional image containing the target region of the lesion with the largest clarity P1 and the corresponding second weight W2 is the highest. As shown in FIG. 4B, the area of the target region 412 in the second cross-sectional image 402 is greater than the area of the target region 414 in the third cross-sectional image 404, and thus the imaging processing module 110 can determine that the region of interest in the three-dimensional volume data 490 is the body data corresponding to the target region 412 in the second cross-sectional image 402. In addition, the imaging processing module 110 can also determine the priority of each cross-sectional image according to the characteristic information of the lesion, for example, according to the blood flow richness of the lesion, the edge integrity of the lesion, and the like. Figure 8 As shown in FIG. 4B, the area of the target region 412 in the second cross-sectional image 402 is greater than the area of the target region 414 in the third cross-sectional image 404, and thus the imaging processing module 110 can determine that the region of interest in the three-dimensional volume data 490 is the body data corresponding to the target region 412 in the second cross-sectional image 402. In addition, the imaging processing module 110 can also determine the priority of each cross-sectional image according to the characteristic information of the lesion, for example, according to the blood flow richness of the lesion, the edge integrity of the lesion, and the like.

[0056] Step 204 : Control the ultrasound probe in the second imaging mode to transmit a second ultrasound wave to the region of interest of the measured tissue at a second preset position.

[0057] When acquiring the three-dimensional volume data of the tested tissue 40, the tested tissue 40 is in a compressed state, which causes the elasticity of the tested tissue 40 to change and the blood supply inside the tested tissue 40 to become abnormal. Therefore, when acquiring the physiological status information of the tested tissue 40, the tested tissue 40 must be in a non-compressed state. Figure 3 The ultrasound imaging system 10 can control the probe 100 to move from the first preset position V1 to the second preset position V2 at the second preset time T2. Alternatively, the user can manually adjust the probe 100 from the first preset position V1 to the second preset position V2 at the second preset time T2. In this embodiment, the probe 100 moves from the first preset position V1 to the second preset position V2 in a direction away from the tissue under test 40, thereby placing the tissue under test 40 in a non-compressed state. The first distance between the first preset position and a reference position of the tissue under test 40 is less than the second distance between the second preset position and the reference position of the tissue under test 40. The reference position can be a location on the tissue under test 40. Taking the breast as an example, the reference position can be the location of the breast close to the chest cavity.

[0058] When the tissue 40 under test is in a non-compressed state, it indicates that the probe 100 is in contact with the tissue 40 under test, or that the pressure between the probe 100 and the tissue 40 is within a preset range. For example, during adjustment, due to movement of the probe 100, it may be necessary to fill the space between the probe 100 and the tissue 40 with coupling agent to ensure good contact between the probe 100 and the surface of the tissue 40 under test. In one embodiment, when the probe 100 is removed from the surface of the tissue 40 under test, sufficient coupling agent or other solid coupling material can be filled between the probe 100 and the tissue 40 under test to ensure that the space between the probe 100 and the tissue 40 under test is in a non-compressed state.

[0059] In this embodiment, after determining the region of interest of the tissue under examination 40, the imaging processing module 110 determines a target position for the transducer 130 on the track 122 based on the region of interest of the tissue under examination 40, and controls the drive mechanism 806 to move the transducer 130 to the target position. When the transducer 130 reaches the target position, the ultrasound imaging system 10 can control the probe 100 to move to the second preset position V2. In other embodiments, the ultrasound imaging system 10 can also control the probe 100 to move to the second preset position V2, and then control the drive mechanism 806 to move the transducer 130 to the target position on the track 122.

[0060] In one embodiment, when the transducer 130 of the probe 100 is a first type transducer:

[0061] Since each volume data in the three-dimensional volume data 490 has a corresponding three-dimensional spatial coordinate value, the transducer 130 moves along the length direction of the track 122 (e.g., Figure 7 When the transducer 130 moves from point o in the positive direction of the X-axis, each position of the transducer 130 on the track 122 also has a corresponding coordinate value. That is, each volume data has corresponding position information of the transducer 130 on the track 122. Therefore, when determining the volume data contained in the region of interest in the cross-sectional image, the imaging processing module 110 can determine the target position of the transducer 130 on the track 122 based on the volume data of the region of interest of the examined tissue 40. Thereafter, the driving mechanism 806 can be used to control the transducer 130 to move to the target position.

[0062] In one embodiment, the imaging processing module 110 determines that the target position of the transducer 130 on the track 122 may be a value according to the region of interest of the tissue under test 40. For example, please refer to Figure 7 If the coordinates of the centroid of the region of interest in the first slice image 400 are (x1, y1, z1), since the first slice image 400 is perpendicular to the direction of movement of the transducer 130, the target position of the transducer 130 on the track 122 corresponding to the region of interest in the first slice image 400 is a single value. For example, the position information of the transducer 130 on the track 122 corresponding to the centroid of the region of interest in the first slice image 400 can be represented as (x1, 0, 0). After the drive mechanism 806 drives the transducer 130 to the target position (x1, 0, 0), the ultrasound imaging system 10 controls the probe 100 to move to the second preset position V2 (e.g., move to the second preset position V2 along the opposite direction of the z-axis) and controls the probe 100 to transmit a second ultrasonic wave toward the region of interest (e.g., the selected region 410) of the tissue being examined 40.

[0063] In one embodiment, the imaging processing module 110 determines that the target position of the transducer 130 on the track 122 may be a range value based on the region of interest of the tissue under test 40. The imaging processing module 110 may obtain a first position of the volume data contained in the region of interest in the moving direction of the transducer 130, and obtain a second position of the volume data contained in the region of interest in the moving direction of the transducer 130; thereafter, the imaging processing module 110 may determine the first position, the second position, or any position between the first position and the second position on the track 122 as the target position. For example, please refer to Figure 8Because the second section image 402 is parallel to the direction of movement of the transducer 130, the imaging processing module 110 determines the target position of the transducer 130 on the track 122 based on the region of interest of the tissue being examined 40, which can be a range of values. If the coordinate values ​​of the volume data for the upper right corner of the target region 412 in the second section image 402 are (x2, y2, z2), and the coordinate values ​​of the volume data for the upper left corner of the target region 412 are (x3, y3, z3), then the position information of the transducer 130 on the track 122 corresponding to the region of interest in the second section image 402 can be represented as a first position (x2, 0, 0) to a second position (x3, 0, 0). Therefore, the driving mechanism 806 can drive the transducer 130 to any position between the first and second positions as the target position, such as the target position (x4, 0, 0), where x4 can be a value within the range of not less than x2 and not greater than x3. After the driving mechanism 806 drives the transducer 130 to move to the target position (x4,0,0), the ultrasound imaging system 10 controls the probe 100 to move to the second preset position V2 (such as moving to the second preset position V2 in the opposite direction of the z-axis), and controls the probe 100 to emit a second ultrasonic wave to the area of ​​interest (such as the selected area 410) of the tissue under test 40.

[0064] In one embodiment, when the transducer 130 of the probe 100 is a second type transducer:

[0065] Because the second-type transducer has array elements 132 arranged in a matrix, the transmitting circuit 102 controls the excitation delay of the array elements of the transducer 130 to cause the probe 100 to generate an ultrasonic wave with a corresponding deflection angle. Therefore, after determining the coordinate value or coordinate value range of the region of interest in the cross-sectional image, the transmitting circuit 102 can generate a second ultrasonic wave with a corresponding deflection angle by setting different excitation delays. For example, when the probe 100 moves to the second preset position V2, the imaging processing module 110 can determine the relative position between the region of interest in the measured tissue 40 and the transducer 130, and based on this relative position, control the excitation delay of the array elements of the transducer 130 to generate a second ultrasonic wave with a corresponding deflection angle, so that the second ultrasonic wave covers the region of interest in the measured tissue 40. In one embodiment, the imaging processing module 110 may obtain a first coordinate value of the region of interest in a preset spatial coordinate system, determine a second coordinate value of the transducer 130 when the probe 100 moves to a second preset position V2, and determine the relative position of the region of interest and the transducer 130 in the tissue under test 40 based on the first and second coordinate values. The second coordinate value of the transducer 130 when the probe 100 moves to the second preset position V2 may be determined using a position sensor (e.g., an accelerometer). After determining the relative position of the region of interest in the tissue under test 40 and the transducer 130, the transmitting circuit 102 may determine the excitation delay of the array elements of the transducer 130 based on the relative position to generate the second ultrasonic wave.

[0066] In this embodiment, after acquiring the three-dimensional volume data 490 of the tested tissue 40, the transducer 130 is located at the end position in the first imaging mode. After determining the target position corresponding to the region of interest, when moving the transducer from the end position to the target position, the transducer 130 can be controlled to move to the target position based on the user's movement operation; or the transducer 130 can be controlled to move to the target position based on the driving operation of the driving mechanism 806.

[0067] When the transducer 130 is controlled to move to the target position based on a user's movement operation, during the user's movement, to facilitate the user's determination of whether the current position has reached the target position, the transmitting circuit 102 may control the transducer 130 to emit a first ultrasonic wave, and the imaging processing module 110 may acquire and display an ultrasonic image of the transducer 130 at the current position during the movement in real time. In this way, the user can determine whether the current position has reached the target position based on the ultrasonic image displayed on the display 112. In one embodiment, the imaging processing module 110 determines the distance between the current position of the transducer 130 and the target position based on the ultrasonic image at the current position and the three-dimensional volumetric data of the examined tissue 40, and controls the output of a prompt message corresponding to the distance information. For example, the imaging processing module 110 may match the ultrasonic image at the current position with the three-dimensional volumetric data of the examined tissue to determine the associated volumetric data corresponding to the ultrasonic image at the current position in the three-dimensional volumetric data. The matching of the ultrasonic image at the current position with the three-dimensional volumetric data of the examined tissue may be achieved using speckle tracking or other matching methods. Since the associated volume data has corresponding spatial coordinate values, the imaging processing module 110 can determine the current position of the transducer 130 corresponding to the associated volume data on the track 122, and determine the distance information based on the difference between the current position and the target position. The display 112 can display the determined distance information. The distance information can be a positive or negative number. For example, for Figure 7 In general, when the distance information is a positive number, it means that the user can move the transducer 130 along the positive direction of the X-axis; when the distance information is a negative number, it means that the user can move the transducer 130 along the negative direction of the X-axis.

[0068] When the drive mechanism 806 controls the transducer 130 to move to the target position, since the target position has already been determined, the drive mechanism 806 can drive the transducer 130 directly to the target position. In one embodiment, the drive mechanism 806 also drives the transducer 130 to a position near the target position, after which the user fine-tunes the position of the transducer 130. During the fine-tuning process, the transmitting circuit 102 can control the transducer 130 to transmit a first ultrasonic wave, and the imaging processing module 110 can capture and display in real time an ultrasonic image of the current position of the transducer 130 during the fine-tuning process, so that the user can easily determine whether the current fine-tuned position is appropriate.

[0069] In this embodiment, during the movement of the probe 100 from the first preset position V1 to the second preset position V2, the imaging processing module 110 may also display a two-dimensional image of the current section in real time on the display 112, making it easier for the user to determine whether the adjustment meets the requirements. After the probe 100 is adjusted, the region of interest may shift slightly due to the change from compression to relaxation of the tissue under test 40. In this case, the user may also manually fine-tune the transducer 130 to move within a small range near the original position. During this movement, the transmitting circuit 102 may control the transducer 130 to transmit a first ultrasonic wave, and the imaging processing module 110 may obtain a three-dimensional ultrasonic image of the transducer 130 during the movement. The imaging processing module 110 may display the three-dimensional ultrasonic image obtained during the movement of the transducer 130, allowing the user to more accurately find the region of interest from the displayed three-dimensional ultrasonic image and then determine the optimal position of the transducer 130 based on the image displayed on the display 112. In one embodiment, after the probe is moved to the second preset position V2, the probe 100 can be controlled to perform a first imaging mode imaging on a sub-region range (three-dimensional body range) with the position of the region of interest as a reference point to obtain three-dimensional volume data of a sub-region range. Subsequently, the shifted position of the region of interest within the sub-region range is further confirmed based on the three-dimensional volume data. The specific determination method can be manually specified by the user, or it can be automatically determined with reference to the method described above, and the transducer is moved accordingly according to the shifted position of the region of interest, so that the probe 100 can subsequently perform a second imaging mode imaging based on the accurate positioning of the region of interest. Afterwards, the imaging processing module 112 can perform other modes of imaging on the region of interest based on the second ultrasound to obtain the required physiological information.

[0070] Step 206: Determine physiological status information of the region of interest of the tested tissue based on the second ultrasound wave.

[0071] In this embodiment, the first imaging mode is the B imaging mode, and the second imaging mode is selected from one or more of a color flow imaging mode, a color Doppler imaging mode, a contrast imaging mode, a compression elastography mode, a shear wave elastography mode, and a vector flow imaging mode. Each second imaging mode can be implemented based on relevant technologies. Thus, at the second preset position V2, the transmitting circuit 102 can control the probe 100 to transmit a second ultrasonic wave toward the region of interest of the tested tissue 40, and convert the second ultrasonic echo returned or reflected by the tested tissue 40 to obtain second ultrasonic echo data, thereby obtaining physiological status information of the region of interest of the tested tissue.

[0072] In this embodiment, during the movement of the probe 100 from the first preset position V1 to the second preset position V2, the region of interest may shift slightly due to the compression and relaxation of the tissue under test 40. To ensure that the probe 100 can continue to image the region of interest in the second imaging mode after the shift, the probe 100 can be controlled to use the position of the region of interest as a reference point and perform the second imaging mode within a sub-region range (three-dimensional volume range) that is guaranteed to contain the region of interest. When performing the second imaging mode within the three-dimensional volume range, the drive mechanism 806 can also control the transducer 130 to move within a small three-dimensional volume range (a small range that can cover the region of interest) to perform multi-modal imaging within the sub-region range near the target position, thereby obtaining various image data within the sub-region range and corresponding physiological status information obtained therefrom. Since the sub-region range can cover the initially determined region of interest, the physiological status information obtained within the sub-region range also includes the physiological status information of the region of interest.

[0073] Therefore, the ultrasound imaging system 10 provides a multimodal system: after completing the full volume imaging mode of the tested tissue 40 in the first imaging mode, it can complete the measurement of other physiological state information of the tested tissue 40 in the second imaging mode, wherein the physiological state information includes but is not limited to blood flow distribution information, blood flow velocity information, tissue hardness information and / or angiography information.

[0074] The above-mentioned ultrasound imaging method acquires a region of interest in three-dimensional volume data of the measured tissue at a first preset position in a first imaging mode, and acquires physiological status information of the region of interest of the measured tissue at a second preset position in a second imaging mode. Furthermore, the full-volume imaging system for non-planar tissue can be applied to other imaging modes to detect physiological status information of the measured tissue, thereby expanding the application range of the full-volume imaging system for non-planar tissue.

[0075] See also Figure 9 , which is a block diagram of an ultrasound imaging system according to another embodiment of the present application. Figure 9 As shown, the ultrasound imaging system 80 can apply the above-mentioned embodiments. The ultrasound imaging system 80 provided by the present application is described below. The ultrasound imaging system 80 may include a processor 800, a storage device 802, a probe 100, a control circuit 804, and a display 112, as well as a computer program (instructions) stored in the storage device 802 and executable on the processor 800. The ultrasound imaging system 80 may also include other hardware components, such as a communication device, a key, a keyboard, etc., which are not described in detail here. The processor 800 can exchange data with the probe 100, the control circuit 804, the storage device 802, and the display 112 via a signal line 808.

[0076] The processor 800 can be a central processing unit (CPU), or other general-purpose processor, digital signal processor (DSP), application-specific integrated circuit (ASIC), field-programmable gate array (FPGA), or other programmable logic device, discrete gate or transistor logic device, discrete hardware component, etc. A general-purpose processor can be a microprocessor or any conventional processor. The processor 800 is the control center of the ultrasound imaging system 80, connecting the various components of the entire ultrasound imaging system 80 using various interfaces and circuits. In this embodiment, the processor 800 can be used to implement all functions of the image processing module 110 and can also integrate the functions of the beamforming module 106 and the signal processing module 108. The specific functions can be referred to and combined with the above embodiments.

[0077] The control circuit 804 may include the functions of the transmitting circuit 102, the receiving circuit 104, the beamforming module 106, and / or the signal processing module 108 in the aforementioned embodiments (i.e., the beamforming module 106 and the signal processing module 108 may be independent circuits). For specific functions, reference may be made to and combined with the aforementioned embodiments.

[0078] The storage device 802 can be used to store the computer programs and / or modules. The processor 800 implements the various functions of the above-mentioned ultrasound imaging method by running or executing the computer programs and / or modules stored in the storage device 802 and calling the data stored in the storage device 802. The storage device 802 can mainly include a program storage area and a data storage area, wherein the program storage area can store an operating system, at least one application required for a function, etc. In addition, the storage device 802 can include a high-speed random access storage device and can also include a non-volatile storage device, such as a hard disk, a memory, a plug-in hard disk, a smart media card (SMC), a secure digital (SD) card, a flash card, at least one magnetic disk storage device, a flash memory device, or other volatile solid-state storage device.

[0079] The probe 100 may include a driving mechanism 806 and a transducer 130 . The driving mechanism 806 may be a motor. The driving mechanism 806 receives driving information from the processor 800 to control the transducer 130 to move in the length direction of the track 122 to obtain three-dimensional volume data of the tissue 40 under test.

[0080] The display 112 can display a user interface (UI), a graphical user interface (GUI), and a cross-sectional image of the tested tissue 40. The ultrasound imaging system 80 can also be used as an input device and an output device. The display 112 can include at least one of a liquid crystal display (LCD), a thin film transistor LCD (TFT-LCD), an organic light emitting diode (OLED) touch display, a flexible touch display, a three-dimensional (3D) touch display, etc.

[0081] The processor 800 reads the executable program code stored in the storage device 802 to run a program corresponding to the executable program code, so as to execute the ultrasonic imaging method in any of the above embodiments.

[0082] In the above embodiments, the description of each embodiment has its own focus. For parts that are not described in detail in a certain embodiment, reference can be made to the relevant descriptions of other embodiments.

[0083] The units described as separate components may or may not be physically separate, and the components shown as units may or may not be physical units, that is, they may be located in one place or distributed across multiple network units. Some or all of these units may be selected to achieve the purpose of this embodiment according to actual needs.

[0084] In addition, the functional units in the various embodiments of the present application may be integrated into a single processing unit, or each unit may exist physically separately, or two or more units may be integrated into a single unit. The aforementioned integrated units may be implemented in the form of hardware or software functional units.

[0085] The above is a detailed introduction to the embodiments of the present application. Specific examples are used herein to illustrate the principles and implementation methods of the present application. The description of the above embodiments is only used to help understand the method and core idea of ​​the present application. At the same time, for those skilled in the art, according to the idea of ​​the present application, there may be changes in the specific implementation methods and application scope. In summary, the content of this specification should not be understood as a limitation on the present application.

Claims

1. An ultrasonic imaging method, applied to an ultrasonic imaging system, characterized in that: The ultrasonic imaging system includes an ultrasonic probe, and the ultrasonic imaging method includes: Controlling the ultrasonic probe in the first imaging mode to transmit a first ultrasonic wave to the measured tissue at a first preset position, and converting the first ultrasonic echo returned by the measured tissue to obtain first ultrasonic echo data; acquiring three-dimensional volume data of the measured tissue based on the first ultrasonic echo data; determining a region of interest of the measured tissue based on the three-dimensional volume data; controlling the ultrasound probe to move from the first preset position to a second preset position, wherein a first distance of the first preset position relative to a reference position of the measured tissue is smaller than a second distance of the second preset position relative to the reference position of the measured tissue; Controlling the ultrasonic probe in the second imaging mode to transmit a second ultrasonic wave to the region of interest of the measured tissue, and converting the second ultrasonic echo returned by the measured tissue to obtain second ultrasonic echo data; determining physiological state information of the region of interest based on the second ultrasound echo data; The controlling the ultrasound probe to move from the first preset position to the second preset position includes: Controlling the ultrasonic probe to move to the second preset position in a direction away from the measured tissue, so that the measured tissue is in a non-compressed state; The controlling the ultrasound probe in the second imaging mode to transmit a second ultrasound wave to the region of interest of the measured tissue comprises: When the measured tissue is in the non-compressed state, the ultrasonic probe at the second preset position is controlled to transmit the second ultrasonic wave to the region of interest of the measured tissue.

2. The ultrasonic imaging method according to claim 1, wherein: When the tissue under test is in a non-compressed state, the ultrasonic probe contacts the tissue under test and the pressure between the ultrasonic probe and the tissue under test is within a preset range.

3. The ultrasonic imaging method according to claim 2, wherein: A liquid coupling agent or a solid coupling material is further included between the ultrasonic probe and the measured tissue.

4. The ultrasonic imaging method according to claim 1, wherein: The probe includes a support assembly and a transducer disposed in the support assembly, the support assembly includes a track, and the transducer is disposed on the track of the support assembly; The controlling the ultrasound probe to move from the first preset position to the second preset position includes: determining a target position of the transducer on the track according to a region of interest of the measured tissue; After controlling the transducer to move to the target position, controlling the ultrasound probe to move from the first preset position to a second preset position; or, After controlling the ultrasound probe to move from the first preset position to the second preset position, determining a target position of the transducer on the track according to a region of interest of the measured tissue; The transducer is controlled to move to the target position.

5. The ultrasonic imaging method according to claim 4, wherein: The three-dimensional volume data includes a plurality of volume data, each volume data having corresponding position information of the transducer on the track, and determining the target position of the transducer on the track according to the region of interest of the measured tissue includes: Acquiring location information corresponding to the volume data contained in the region of interest; The target position of the transducer on the track is determined according to the position information of the volume data contained in the region of interest.

6. The ultrasonic imaging method according to claim 5, wherein: The step of determining a target position of the transducer on the track according to position information of the volume data included in the region of interest includes: Acquire a first position of volume data contained in the region of interest in a moving direction of the transducer; Acquire a second position of the volume data contained in the region of interest in the moving direction of the transducer; The first position, the second position, or any position between the first position and the second position on the track is determined as the target position.

7. The ultrasonic imaging method according to claim 4, wherein: The ultrasonic probe includes a driving mechanism, and controlling the transducer to move to the target position includes: Controlling the transducer to move to the target position based on a user's movement operation; or The transducer is controlled to move to the target position based on the driving operation of the driving mechanism.

8. The ultrasonic imaging method according to claim 7, wherein: The controlling the transducer to move to the target position based on the user's movement operation includes: In the process of moving the transducer to the target position based on the user's movement operation, the transducer is controlled to emit the first ultrasonic wave, and an ultrasonic image of the current position of the transducer during the movement is acquired and displayed in real time.

9. The ultrasonic imaging method according to claim 8, wherein: After acquiring and displaying the ultrasonic image of the current position of the transducer during the movement in real time, the method further includes: determining distance information between the current position of the transducer and the target position based on the ultrasound image of the current position and the three-dimensional volume data of the measured tissue; Control output of prompt information corresponding to the distance information.

10. The ultrasonic imaging method according to claim 7, wherein: The step of controlling the transducer to move to the target position based on the driving operation of the driving mechanism includes: The driving mechanism is controlled to drive the transducer to move to the target position.

11. The ultrasonic imaging method according to claim 10, wherein: The controlling the driving mechanism to drive the transducer to move to the target position includes: The driving mechanism is controlled to drive the transducer to move from an end position in the first imaging mode to the target position.

12. The ultrasonic imaging method according to claim 7, wherein: After controlling the transducer to move to the target position based on the driving operation of the driving mechanism, the method further includes: An operation of finely adjusting the position of the transducer at the target position is performed based on a user's movement operation.

13. The ultrasonic imaging method according to claim 1, wherein: The probe includes a support assembly and a transducer disposed in the support assembly, wherein the transducer includes a plurality of array elements arranged in a planar array; and controlling the ultrasound probe in the second imaging mode to transmit a second ultrasound wave to a region of interest of the measured tissue includes: determining a relative position of the region of interest and the transducer; The excitation delay of the array elements of the transducer is controlled based on the relative position to generate the second ultrasonic wave with a corresponding deflection angle.

14. The ultrasonic imaging method according to claim 13, wherein: The three-dimensional volume data includes a plurality of volume data, each volume data having a coordinate value corresponding to a preset spatial coordinate system, and determining the relative position of the region of interest and the transducer includes: Obtaining a first coordinate value of the region of interest in the preset spatial coordinate system; determining a second coordinate value of the transducer when the probe moves to the second preset position; The relative position is determined based on the first coordinate value and the second coordinate value.

15. The ultrasonic imaging method according to claim 1, wherein: After controlling the ultrasound probe to move from the first preset position to the second preset position, the method further includes: controlling the ultrasound probe at the second preset position to transmit a first ultrasound wave to a subregion of the measured tissue including the region of interest in the first imaging mode, and acquiring three-dimensional volume data of the subregion of the measured tissue; Determining a shifted position of the region of interest within the subregion based on the three-dimensional volume data of the subregion; and The ultrasound probe in the second imaging mode is controlled to transmit a second ultrasound wave to the region of interest at the shifted position, and physiological state information of the region of interest at the shifted position is determined.

16. The ultrasonic imaging method according to claim 1, wherein: After controlling the ultrasound probe to move from the first preset position to the second preset position, the method further includes: Control the ultrasound probe at the second preset position to transmit a second ultrasonic wave to the sub-region range of the tested tissue including the region of interest in the second imaging mode, and obtain physiological status information of the sub-region range of the tested tissue; wherein the physiological status information of the sub-region range of the tested tissue includes the physiological status information of the region of interest.

17. The ultrasonic imaging method according to claim 1, wherein: The ultrasound imaging system includes an input interface, and determining the region of interest of the measured tissue based on the three-dimensional volume data includes: receiving an input operation from a user via the input interface; Determine the region of interest based on the input operation; or determining a target region containing a lesion in the three-dimensional volume data based on the processing model; The target region is determined to be the region of interest.

18. The ultrasonic imaging method according to claim 17, wherein: The ultrasound imaging system includes a display, and determining the region of interest based on the input operation includes: Controlling the display of a section image corresponding to a preset position in the three-dimensional volume data; receiving a user's selection of a selected area in the cross-sectional image; The volume data included in the selected region is determined to be the region of interest.

19. The ultrasonic imaging method according to claim 17, wherein: The determining, based on the processing model, a target region containing a lesion in the three-dimensional volume data comprises: Controlling a slicing operation on the three-dimensional volume data to obtain a first preset number of slice images; determining, based on the processing model, a second preset number of cross-sectional images of the target area including lesions in the first preset number; The determining that the target area is the area of ​​interest includes: According to a preset rule, a target region included in the slice image with the highest priority among the second preset number is selected as the region of interest.

20. The ultrasonic imaging method according to claim 19, wherein: The preset rules include one or more of the size of the target region containing the lesion or the clarity of the target region containing the lesion.

21. The ultrasonic imaging method according to claim 19, wherein: The determining, based on the processing model, a second preset number of cross-sectional images of the target area containing lesions in the first preset number comprises: Determining a second preset number of cross-sectional images of the target area containing lesions in the first preset number based on an image segmentation model; or; A second preset number of cross-sectional images of the target area including the lesion in the first preset number are determined based on the learning model.

22. The ultrasonic imaging method according to claim 1, wherein: The ultrasound probe includes transducers arranged in a linear array or in a matrix array.

23. The ultrasonic imaging method according to any one of claims 1 to 22, wherein: The first imaging mode is a B imaging mode, and the second imaging mode is selected from one or more of a color flow imaging mode, a color Doppler imaging mode, an angiography imaging mode, a compression elastic imaging mode, a shear wave elastic imaging mode, and a vector flow imaging mode.

24. The ultrasonic imaging method according to any one of claims 1 to 22, wherein: The physiological status information includes blood flow distribution information, blood flow velocity information, tissue hardness information and / or angiography information.

25. An ultrasonic imaging method, applied to an ultrasonic imaging system, characterized in that: The ultrasonic imaging system includes an ultrasonic probe, and the ultrasonic imaging method includes: Acquiring three-dimensional volume data of the measured tissue collected by the ultrasound probe in the first imaging mode at a first preset position; determining a region of interest of the measured tissue based on the three-dimensional volume data of the measured tissue; Controlling the ultrasound probe to move from a first preset position to a second preset position, wherein a first distance of the first preset position relative to a reference position of the measured tissue is smaller than a second distance of the second preset position relative to the reference position of the measured tissue; controlling the ultrasound probe in the second imaging mode to transmit ultrasound waves to the region of interest of the measured tissue at the second preset position, and converting ultrasound echoes returned by the measured tissue to obtain ultrasound echo data; determining physiological state information of the region of interest based on the ultrasound echo data; Wherein, controlling the ultrasound probe to move from the first preset position to the second preset position includes: Controlling the ultrasonic probe to move to the second preset position in a direction away from the measured tissue, so that the measured tissue is in a non-compressed state; The controlling the ultrasound probe in the second imaging mode to transmit a second ultrasound wave to the region of interest of the measured tissue comprises: When the measured tissue is in the non-compressed state, the ultrasonic probe at the second preset position is controlled to transmit the second ultrasonic wave to the region of interest of the measured tissue.

26. An ultrasonic imaging system, characterized in that: include: Full volume probe, selectively working in the first imaging mode or the second imaging mode; a processor connected to the full-volume probe, the processor being configured to control the full-volume probe in the first imaging mode to transmit a first ultrasonic wave toward the measured tissue, and convert the first ultrasonic echo received back from the measured tissue to obtain first ultrasonic echo data; the processor acquiring three-dimensional volume data of the measured tissue based on the first ultrasonic echo data, and determining a region of interest of the measured tissue based on the three-dimensional volume data; the processor being configured to control the full-volume probe in the second imaging mode to transmit a second ultrasonic wave toward the region of interest of the measured tissue, and convert the second ultrasonic echo received back from the measured tissue to obtain second ultrasonic echo data; and the processor further determining physiological status information of the region of interest based on the second ultrasonic echo data; wherein, a first preset position of the full-volume probe relative to a reference position of the measured tissue in the first imaging mode is smaller than a second preset position of the full-volume probe relative to a reference position of the measured tissue in the second imaging mode; wherein, when controlling the full-volume probe in the second imaging mode to transmit a second ultrasonic wave toward a region of interest of the measured tissue, the processor controls the full-volume probe to move away from the measured tissue to the second preset position so that the measured tissue is in a non-compressed state; when the measured tissue is in the non-compressed state, the processor controls the full-volume probe at the second preset position to transmit a second ultrasonic wave toward the region of interest of the measured tissue.

27. The ultrasound imaging system according to claim 26, wherein: When the measured tissue is in a non-compressed state, the full volume probe is in contact with the measured tissue and the pressure between the full volume probe and the measured tissue is within a preset range.

28. The ultrasound imaging system according to claim 27, wherein: A liquid coupling agent or a solid coupling material is further included between the full volume probe and the measured tissue.

29. The ultrasound imaging system according to claim 26, wherein: The probe includes a support assembly and a transducer arranged in the support assembly, the support assembly includes a track, the transducer is arranged on the track of the support assembly, and the processor determines the target position of the transducer on the track based on the region of interest of the tested tissue; the processor is also used to control the transducer to move to the target position and control the full volume probe to move from the first preset position to the second preset position.

30. The ultrasound imaging system of claim 29, wherein: The three-dimensional volume data includes a plurality of volume data, each volume data having corresponding position information of the transducer on the track. When determining the target position of the transducer on the track based on the region of interest of the measured tissue, the processor is used to obtain the position information corresponding to the volume data contained in the region of interest. The processor also determines the target position of the transducer on the track based on the position information of the volume data contained in the region of interest.

31. The ultrasound imaging system of claim 30, wherein: When determining the target position of the transducer on the track based on the position information of the volume data contained in the region of interest, the processor is used to obtain the first position of the volume data contained in the region of interest in the direction of movement of the transducer, and obtain the second position of the volume data contained in the region of interest in the direction of movement of the transducer; the processor is also used to determine the first position, the second position, or any position between the first position and the second position on the track as the target position.

32. The ultrasound imaging system of claim 29, wherein: The full volume probe includes a driving mechanism. When controlling the transducer to move to the target position, the processor controls the transducer to move to the target position based on a movement operation of a user, or the processor controls the transducer to move to the target position based on a driving operation of the driving mechanism.

33. The ultrasound imaging system of claim 32, wherein: When the transducer is controlled to move to the target position based on the user's movement operation, during the process of the user moving the transducer to the target position, the processor controls the transducer to emit the first ultrasonic wave, and acquires and displays the ultrasonic image of the current position of the transducer during the movement in real time.

34. The ultrasound imaging system of claim 33, wherein: After acquiring and displaying in real time an ultrasonic image of the current position of the transducer during movement, the processor further determines distance information between the current position of the transducer and the target position based on the ultrasonic image of the current position and the three-dimensional volume data of the measured tissue; The processor is used to control the output of prompt information corresponding to the distance information.

35. The ultrasound imaging system of claim 32, wherein: When the transducer is controlled to move to the target position based on the driving operation of the driving mechanism, the processor controls the driving mechanism to drive the transducer to move to the target position.

36. The ultrasound imaging system of claim 35, wherein: When controlling the driving mechanism to drive the transducer to move to the target position, the processor controls the driving mechanism to drive the end position of the transducer in the first imaging mode to move to the target position.

37. The ultrasound imaging system of claim 32, wherein: After controlling the transducer to move to the target position based on the driving operation of the driving mechanism, the processor further performs a fine adjustment operation of the position of the transducer at the target position based on a movement operation of a user.

38. The ultrasound imaging system of claim 26, wherein: The probe includes a support assembly and a transducer disposed within the support assembly, wherein the transducer includes a plurality of array elements arranged in a planar array. When controlling the full-volume probe in a second imaging mode to transmit a second ultrasonic wave toward a region of interest of the measured tissue, the processor is configured to determine a relative position of the region of interest relative to the transducer, and based on the relative position, control the excitation delay of the array elements of the transducer to generate the second ultrasonic wave having a corresponding deflection angle.

39. The ultrasound imaging system of claim 38, wherein: The three-dimensional volume data includes a plurality of volume data, each volume data having a coordinate value corresponding to a preset spatial coordinate system. When determining the relative position of the region of interest relative to the transducer, the processor is configured to obtain a first coordinate value of the region of interest in the preset spatial coordinate system and determine a second coordinate value when the transducer moves to the second preset position; the processor further determines the relative position based on the first coordinate value and the second coordinate value.

40. The ultrasound imaging system of claim 26, wherein: The ultrasound imaging system includes an input interface, and when determining the region of interest of the measured tissue based on the three-dimensional volume data, the processor receives a user input operation through the input interface and determines the region of interest based on the input operation; Alternatively, the processor determines a target region containing a lesion in the three-dimensional volume data based on a processing model, and determines the target region as the region of interest.

41. The ultrasound imaging system of claim 40, wherein: The ultrasound imaging system includes a display. When the region of interest is determined based on the input operation, the processor controls the display of a section image corresponding to a preset position in the three-dimensional volume data. The processor is also used to receive a user selection of a selected region in the section image and determine that the volume data contained in the selected region is the region of interest.

42. The ultrasound imaging system of claim 40, wherein: When determining, based on the processing model, a target area containing a lesion in the three-dimensional volume data, the processor controls a slicing operation on the three-dimensional volume data to obtain a first preset number of slice images; the processor determines, based on the processing model, a second preset number of slice images of the target area containing the lesion in the first preset number, and the processor further selects a slice image with a highest priority from the second preset number according to a preset rule.

43. The ultrasound imaging system of claim 42, wherein: The preset rules include one or more of the size of the target region containing the lesion or the clarity of the target region containing the lesion.

44. The ultrasound imaging system of claim 42, wherein: When determining the second preset number of cross-sectional images of the target area containing lesions in the first preset number based on the processing model, the processor determines the second preset number of cross-sectional images of the target area containing lesions in the first preset number based on the image segmentation model; or, the processor determines the second preset number of cross-sectional images of the target area containing lesions in the first preset number based on the learning model.

45. The ultrasound imaging system of claim 26, wherein: The full volume probe includes transducers arranged in a linear array or in a matrix array.

46. ​​The ultrasound imaging system according to any one of claims 26 to 45, wherein: The first imaging mode is B imaging mode, and the second imaging mode is selected from B imaging mode, color flow imaging mode, color Doppler imaging mode, angiography mode, compression elastic imaging mode, shear wave elastic imaging mode and vector flow imaging mode.

47. The ultrasound imaging system according to any one of claims 26 to 45, wherein: The physiological status information includes blood flow distribution information, blood flow velocity information, tissue hardness information and / or angiography information.

48. A computer-readable storage medium storing computer instructions, characterized in that: When the computer instructions are executed by a processor, the ultrasound imaging method according to any one of claims 1 to 25 is implemented.

Images