Elastographic method and ultrasound imaging system

Abstract

An elastography method (200) and an ultrasound imaging system. The method (200) comprises: transmitting a first push pulse to a target tissue to generate a first shear wave (S210); transmitting a first ultrasound wave tracking the first shear wave and receiving a first ultrasound echo to obtain first ultrasound echo data (S220); generating a first elastography image based on the first ultrasound echo data (S230); determining a target region in the first elastography image (S240); transmitting a second push pulse based on the target region to generate a second shear wave propagating in a target sub-tissue corresponding to the target region (S250); transmitting a second ultrasound wave tracking the second shear wave and receiving a second ultrasound echo to obtain second ultrasound echo data, wherein the second ultrasound wave has a greater penetration than the first ultrasound wave and / or the second shear wave has a greater penetration than the first shear wave (S260); generating a second elastography image based on the second ultrasound echo data (S270); and outputting the second elastography image (S280). The method (200) can solve the problem of insufficient penetration in the elastography process.

Description

[0001] Divisional application information This invention patent application is a divisional application of the application filed on January 6, 2021, with application number 202180079842.9, and the invention patent application entitled "Elastography Method and Ultrasonic Imaging System". Technical Field

[0002] This application relates to the field of ultrasound imaging technology, and more specifically to an elastography method and an ultrasound imaging system. Background Technology

[0003] Ultrasound elastography is an ultrasound imaging technique aimed at extracting parameters related to tissue stiffness. In recent years, it has been widely applied in clinical research and diagnosis. Currently, ultrasound elastography is commonly used to examine the thyroid gland, breast, muscles and bones, liver, and blood vessels. Assessing tissue stiffness can effectively assist in the early detection of lesions, differentiation of benign and malignant tumors, and evaluation of postoperative recovery.

[0004] Shear wave elastography generates acoustic radiation force by emitting special ultrasound pulses into the tissue, creating a shear wave source within the tissue and generating shear waves that propagate within the tissue. By identifying and detecting the propagation information of the shear waves within the tissue using ultrasound, quantitative parameters such as shear wave propagation velocity and Young's modulus can be calculated for imaging. This allows for quantitative elastography of the tissue and is one of the most widely used and closely followed elastography methods by doctors.

[0005] In many clinical cases, the target tissue has high hardness, resulting in rapid attenuation of shear waves. For example, breast cancer lesions are typically not only hard (most exceeding 100 kPa, even reaching 300-400 kPa), but also large in area. Within such lesions, shear wave sources are not easily generated; even if they are generated, the amplitude of shear waves is very weak and cannot easily propagate through the entire lesion area, thus causing inaccurate or incomplete elasticity measurements, resulting in voids in the elasticity image and severely impacting the user experience. Summary of the Invention

[0006] The summary section introduces a series of simplified concepts, which will be further explained in detail in the detailed description section. The summary section of this invention is not intended to limit the key features and essential technical features of the claimed technical solution, nor is it intended to determine the scope of protection of the claimed technical solution.

[0007] A first aspect of this application provides an elastic imaging method, the method comprising: A first push pulse is emitted toward the target tissue of the object being tested to generate a first shear wave propagating within the target tissue; A first ultrasonic wave that tracks the first shear wave is emitted toward the target tissue, and a first ultrasonic echo returned by the target tissue is received to obtain first ultrasonic echo data; A first elasticity image of the target tissue is generated based on the first ultrasound echo data; In the first elastic image, a target region that meets the preset conditions is determined; A second push pulse is emitted toward the target tissue based on the target region to generate a second shear wave propagating within the target sub-tissue corresponding to the target region; A second ultrasonic wave that tracks the second shear wave is emitted toward the target tissue, and the second ultrasonic echo returned by the target tissue is received to obtain the second ultrasonic echo data of the target sub-tissue; wherein, the penetrating power of the second ultrasonic wave to the target sub-tissue is greater than the penetrating power of the first ultrasonic wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than the penetrating power of the first shear wave to the target sub-tissue; A second elasticity image of the target sub-tissue is generated based on the second ultrasound echo data; Output the second elastic image.

[0008] A second aspect of this application provides an elastic imaging method, the method comprising: A first elastic image and a first tissue structure image of the target tissue of the test object are acquired. The first elastic image and the first tissue structure image correspond to the same tissue cross section. The first elastic image is obtained by detecting a first ultrasonic wave of a first shear wave propagating in the target tissue and based on a first ultrasonic echo of the first ultrasonic wave. In the first elastic image or the first tissue structure image, a target region that meets the preset conditions is determined; A push pulse is emitted toward the target tissue based on the target region to generate a second shear wave propagating within the target sub-tissue corresponding to the target region; A second ultrasonic wave that tracks the second shear wave is emitted toward the target tissue, and the second ultrasonic echo returned by the target tissue is received to obtain the second ultrasonic echo data of the target sub-tissue; wherein, the penetrating power of the second ultrasonic wave to the target sub-tissue is greater than the penetrating power of the first ultrasonic wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than the penetrating power of the first shear wave to the target sub-tissue; A second elastic image of the target sub-tissue is obtained based on the second ultrasound echo data; Output the second elastic image.

[0009] A third aspect of this application provides an elastic imaging method, the method comprising: The option provides at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponds to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponds to a second push pulse and a second ultrasound. When a command to select a second elastic imaging mode is received, a second push pulse is emitted toward the target tissue of the object under test to generate a second shear wave propagating within the target tissue; A second ultrasonic wave that tracks the second shear wave is emitted toward the target tissue, and the ultrasonic echo returned by the target tissue is received to obtain ultrasonic echo data; wherein, the penetrating power of the second ultrasonic wave to the target tissue is greater than the penetrating power of the first ultrasonic wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first driving pulse to the target tissue; A second elastic image of the target tissue is obtained based on the ultrasound echo data; Output the second elastic image.

[0010] A fourth aspect of this application provides an elastic imaging method, the method comprising: Acquire a first ultrasound image of the target tissue of the tested object, wherein the first ultrasound image includes a tissue structure image; In the first ultrasound image, a target region that meets the preset conditions is identified; The option provides at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponds to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponds to a second push pulse and a second ultrasound. In the second elastic imaging mode, a first push pulse is emitted toward the target tissue based on the target region to generate a second shear wave propagating within the target tissue; A second ultrasonic wave that tracks the second shear wave is emitted toward the target tissue, and the ultrasonic echo returned by the target tissue is received to obtain ultrasonic echo data; wherein, the penetrating power of the second ultrasonic wave to the target tissue is greater than the penetrating power of the first ultrasonic wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first driving pulse to the target tissue; An elasticity image of the target tissue is obtained based on the ultrasound echo data; Output the elastic image.

[0011] A fifth aspect of this application provides an ultrasound imaging system, the ultrasound imaging system comprising: Ultrasonic probe; The transmitting circuit is used to excite the ultrasound probe to emit a first push pulse toward the target tissue of the object being measured, so as to generate a first shear wave propagating within the target tissue; and to excite the ultrasound probe to emit a first ultrasound wave that tracks the first shear wave toward the target tissue. A receiving circuit is used to control the ultrasound probe to receive the first ultrasound echo returned by the target tissue in order to obtain first ultrasound echo data. Processor, used for: A first elasticity image of the target tissue is generated based on the first ultrasound echo data; In the first elastic image, a target region that meets the preset conditions is determined; The transmitting circuit is also used to excite the ultrasound probe to emit a second push pulse toward the target tissue based on the target region, so as to generate a second shear wave propagating within the target sub-tissue corresponding to the target region; and to excite the ultrasound probe to emit a second ultrasound wave that tracks the second shear wave toward the target tissue; The receiving circuit is further configured to receive the second ultrasonic echo returned by the target tissue to obtain the second ultrasonic echo data of the target sub-tissue; wherein the penetrating power of the second ultrasonic wave to the target sub-tissue is greater than the penetrating power of the first ultrasonic wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than the penetrating power of the first shear wave to the target sub-tissue; The processor is also configured to generate a second elasticity image of the target sub-tissue based on the second ultrasound echo data; A display for showing the second elastic image.

[0012] A sixth aspect of this application provides an ultrasound imaging system, the ultrasound imaging system comprising: Processor, used for: A first elastic image and a first tissue structure image of the target tissue of the test object are acquired. The first elastic image and the first tissue structure image correspond to the same tissue cross section. The first elastic image is obtained by detecting a first ultrasonic wave of a first shear wave propagating in the target tissue and based on a first ultrasonic echo of the first ultrasonic wave. In the first elastic image or the first tissue structure image, a target region that meets the preset conditions is determined; The transmitting circuit is used to excite the ultrasound probe to emit a push pulse toward the target sub-tissue based on the target region, so as to generate a second shear wave propagating within the target sub-tissue corresponding to the target region; and to excite the ultrasound probe to emit a second ultrasound wave that tracks the second shear wave toward the target tissue; A receiving circuit is used to control the ultrasound probe to receive the second ultrasound echo returned by the target tissue, so as to obtain the second ultrasound echo data of the target self-organization; wherein, the penetrating power of the second ultrasound wave to the target sub-tissue is greater than the penetrating power of the first ultrasound wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than the penetrating power of the first shear wave to the target sub-tissue; The processor is also configured to obtain a second elasticity image of the target sub-tissue based on the second ultrasound echo data; A display for showing the second elastic image.

[0013] A seventh aspect of this application provides an ultrasound imaging system, the ultrasound imaging system comprising: A human-computer interaction device for providing options for at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponding to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponding to a second push pulse and a second ultrasound. The transmitting circuit is configured to, upon receiving a selection instruction for a second elastic imaging mode, excite an ultrasound probe to emit a second push pulse toward the target tissue of the object being measured to generate a second shear wave propagating within the target tissue; and excite the ultrasound probe to emit a second ultrasound wave that tracks the second shear wave toward the target tissue. A receiving circuit is used to receive the ultrasonic echo returned by the target tissue to obtain ultrasonic echo data; wherein the penetrating power of the second ultrasonic wave to the target tissue is greater than the penetrating power of the first ultrasonic wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first pushing pulse to the target tissue; A processor for obtaining an elastic image of the target tissue based on the ultrasound echo data; A display for outputting the elastic image.

[0014] An eighth aspect of this application provides an ultrasound imaging system, the ultrasound imaging system comprising: A processor is configured to acquire a first ultrasound image of a target tissue of a test object, wherein the first ultrasound image includes a tissue structure image; the processor is further configured to determine a target region in the first ultrasound image that meets preset conditions. A human-computer interaction device for providing options for at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponding to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponding to a second push pulse and a second ultrasound. The transmitting circuit is configured to, in the second elastography mode, excite an ultrasound probe to emit a second push pulse toward the target tissue based on the target region to generate a second shear wave propagating within the target tissue; and excite the ultrasound probe to emit a second ultrasound wave toward the target tissue that tracks the second shear wave. A receiving circuit is used to control the ultrasound probe to receive the ultrasound echo returned by the target tissue to obtain ultrasound echo data; wherein, the penetrating power of the second ultrasound wave to the target tissue is greater than the penetrating power of the first ultrasound wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first pushing pulse to the target tissue; The processor is also configured to obtain an elastic image of the target tissue based on the ultrasound echo data; A display for outputting the elastic image.

[0015] The elastography method and ultrasound imaging system according to the embodiments of this application can achieve high-penetration elastography, solving the problem of inaccurate measurement or voids caused by insufficient penetration during elastography. Attached Figure Description

[0016] Figure 1 A schematic block diagram of an ultrasound imaging system according to an embodiment of this application is shown; Figure 2 This is a schematic flowchart of an elastic imaging method according to an embodiment of this application; Figure 3A , Figure 3B This is a schematic diagram of a first elastic image according to an embodiment of the present application; Figure 4 A schematic diagram showing the determination of a target region based on a first elastic image according to an embodiment of this application is shown; Figure 5 A schematic diagram illustrating the determination of a target region based on the credibility of a first elastic image according to an embodiment of this application is shown; Figure 6 A schematic diagram illustrating the determination of a target region based on a tissue structure image corresponding to a first elastic image, according to an embodiment of this application, is shown. Figure 7A schematic diagram of the sound field of a first driving pulse and a second driving pulse according to an embodiment of this application is shown; Figure 8 A schematic diagram of the sound field of a first driving pulse and a second driving pulse according to another embodiment of this application is shown; Figure 9 A schematic diagram of the sound field of a second driving pulse according to an embodiment of this application is shown; Figure 10 A schematic diagram of the sound field boundaries of a first ultrasonic wave and a second ultrasonic wave according to an embodiment of this application is shown. Figure 11 A schematic diagram of a first elastic image and a second elastic image according to an embodiment of this application is shown; Figure 12 This is a schematic flowchart of an elastic imaging method according to another embodiment of this application; Figure 13 This is a schematic flowchart of an elastic imaging method according to yet another embodiment of this application; Figure 14 This is a schematic flowchart of an elastic imaging method according to another embodiment of the present application. Detailed Implementation

[0017] To make the objectives, technical solutions, and advantages of this application more apparent, exemplary embodiments according to this application will be described in detail below with reference to the accompanying drawings. Obviously, the described embodiments are merely some embodiments of this application, and not all embodiments of this application. It should be understood that this application is not limited to the exemplary embodiments described herein. Based on the embodiments of this application described herein, all other embodiments obtained by those skilled in the art without inventive effort should fall within the protection scope of this application.

[0018] The following description provides numerous specific details to offer a more thorough understanding of this application. However, it will be apparent to those skilled in the art that this application can be practiced without one or more of these details. In other instances, certain technical features well-known in the art have not been described to avoid confusion with this application.

[0019] It should be understood that this application can be implemented in various forms and should not be construed as being limited to the embodiments set forth herein. Rather, providing these embodiments will make the disclosure thorough and complete, and will fully convey the scope of this application to those skilled in the art.

[0020] The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the scope of this application. When used herein, the singular forms “a,” “an,” and “the” are also intended to include the plural forms unless the context clearly indicates otherwise. It should also be understood that the terms “comprising” and / or “including,” when used in this specification, identify the presence of the stated features, integers, steps, operations, elements, and / or components, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and / or groups. When used herein, the term “and / or” includes any and all combinations of the associated listed items.

[0021] To fully understand this application, detailed steps and structures will be presented in the following description to illustrate the technical solutions proposed in this application. Preferred embodiments of this application are described in detail below; however, in addition to these detailed descriptions, this application may have other implementation methods.

[0022] To fully understand this application, a detailed structure will be presented in the following description to illustrate the technical solution proposed in this application. Optional embodiments of this application are described in detail below; however, in addition to these detailed descriptions, this application may have other implementation methods.

[0023] Below, first refer to Figure 1 An ultrasound imaging system according to an embodiment of this application is described. Figure 1 A schematic structural block diagram of an ultrasound imaging system 100 according to an embodiment of this application is shown.

[0024] like Figure 1 As shown, the ultrasound imaging system 100 includes an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116, and a display 118. Further, the ultrasound imaging system may also include a transmit / receive selection switch 120 and a beamforming module 122. The transmitting circuit 112 and the receiving circuit 114 can be connected to the ultrasound probe 110 via the transmit / receive selection switch 120.

[0025] The ultrasound probe 110 includes multiple transducer elements. These elements can be arranged in a row to form a linear array, or in a two-dimensional matrix to form a planar array. They can also form a convex array. Each transducer element is used to emit ultrasonic waves based on an excitation electrical signal, or to convert received ultrasonic waves into electrical signals. Therefore, each transducer element can be used to achieve the mutual conversion between electrical pulse signals and ultrasonic waves, thereby enabling the emission of ultrasonic waves to the target tissue area of ​​the object being measured, and also to receive ultrasonic echoes reflected back from the tissue. During shear wave elastography, the transducer elements in the ultrasound probe 110 are used to emit a driving pulse towards the target tissue to generate shear waves propagating within the target tissue. The transducer elements in the ultrasound probe 110 are also used to emit ultrasonic waves that track the shear waves towards the target tissue, and to receive ultrasonic echoes. The transmission and reception sequences can be used to control which transducer elements are used to emit ultrasonic waves and which are used to receive ultrasonic waves, or to control the transducer elements to be used in time-slotted manner for emitting ultrasonic waves or receiving ultrasonic echoes. Transducer array elements involved in ultrasonic wave emission can be simultaneously excited by electrical signals to emit ultrasonic waves at the same time; or, transducer array elements involved in ultrasonic beam emission can be excited by several electrical signals with a certain time interval to continuously emit ultrasonic waves with a certain time interval.

[0026] During ultrasound imaging, the transmitting circuit 112 sends a delayed-focused transmission pulse to the ultrasound probe 110 via the transmit / receive selection switch 120. Excited by the transmission pulse, the ultrasound probe 110 emits an ultrasonic beam towards the tissue of the target area of ​​the object being measured. After a certain delay, it receives the ultrasonic echo reflecting back from the tissue of the target area, carrying tissue information, and converts this ultrasonic echo back into an electrical signal. The receiving circuit 114 receives the electrical signal converted by the ultrasound probe 110, obtains the ultrasonic echo signal, and sends these ultrasonic echo signals to the beamforming module 122. The beamforming module 122 performs focusing delay, weighting, and channel summation on the ultrasonic echo data, and then sends it to the processor 116. The processor 116 performs signal detection, signal enhancement, data conversion, and logarithmic compression on the ultrasonic echo signal to form an ultrasound image, such as a tissue structure image or an elasticity image. The ultrasound image obtained by the processor 116 can be displayed on the display 118 or stored in the memory 124.

[0027] Optionally, the processor 116 can be implemented as software, hardware, firmware, or any combination thereof, and can use one or more application-specific integrated circuits (ASICs), one or more general-purpose integrated circuits, one or more microprocessors, one or more programmable logic devices, or any combination of the foregoing circuits and / or devices, or other suitable circuits or devices. Furthermore, the processor 116 can control other components in the ultrasound imaging system 100 to perform the corresponding steps of the methods in the various embodiments of this specification.

[0028] The display 118 is connected to the processor 116. The display 118 can be a touch screen, an LCD screen, etc.; or, the display 118 can be an independent display such as an LCD screen or a television, separate from the ultrasound imaging system 100; or, the display 118 can be the screen of an electronic device such as a smartphone or tablet, etc. The number of displays 118 can be one or more. For example, the display 118 may include a main screen and a touch screen, with the main screen primarily used to display ultrasound images and the touch screen primarily used for human-computer interaction.

[0029] The display 118 can display the ultrasound images obtained by the processor 116. Furthermore, while displaying the ultrasound images, the display 118 can also provide a graphical user interface for human-machine interaction. One or more controlled objects can be set on the graphical interface, allowing the user to input operation commands using a human-machine interaction device to control these controlled objects and perform corresponding control operations. For example, icons can be displayed on the graphical interface, and the human-machine interaction device can be used to operate these icons to perform specific functions, such as drawing a region of interest bounding box on the ultrasound image.

[0030] Optionally, the ultrasound imaging system 100 may also include other human-machine interface devices besides the display 118, which are connected to the processor 116. For example, the processor 116 may be connected to the human-machine interface device via an external input / output port, which may be a wireless communication module, a wired communication module, or a combination of both. The external input / output port may also be based on USB, bus protocols such as CAN, and / or wired network protocols.

[0031] The human-computer interaction device may include an input device for detecting user input information. This input information may be, for example, control commands for the timing of ultrasound transmission / reception, operational input commands for drawing points, lines, or boxes on an ultrasound image, or other types of commands. The input device may include one or a combination of several of the following: a keyboard, mouse, scroll wheel, trackball, mobile input device (e.g., a mobile device with a touchscreen, a mobile phone, etc.), a multi-function knob, etc. The human-computer interaction device may also include an output device such as a printer.

[0032] The ultrasound imaging system 100 may also include a memory 124 for storing instructions executed by the processor, storing received ultrasound echoes, storing ultrasound images, etc. The memory may be a flash memory card, solid-state memory, hard disk, etc. It may be volatile and / or non-volatile memory, removable memory and / or non-removable memory, etc.

[0033] It should be understood that Figure 1 The components included in the ultrasound imaging system 100 shown are merely illustrative and may include more or fewer components. This application is not limiting in this regard.

[0034] Below, we will refer to Figure 2 This application describes an elastic imaging method according to an embodiment of the present application. Figure 2 This is a schematic flowchart of an elastic imaging method 200 according to an embodiment of this application.

[0035] like Figure 2 As shown, an embodiment of the elastic imaging method 200 of this application includes the following steps: In step S210, a first push pulse is emitted toward the target tissue of the object under test to generate a first shear wave propagating within the target tissue; In step S220, a first ultrasonic wave that tracks the first shear wave is emitted to the target tissue, and a first ultrasonic echo returned by the target tissue is received to obtain first ultrasonic echo data. In step S230, a first elasticity image of the target tissue is generated based on the first ultrasound echo data; In step S240, a target region that meets the preset conditions is determined in the first elastic image; In step S250, a second push pulse is emitted toward the target tissue based on the target region to generate a second shear wave propagating within the target sub-tissue corresponding to the target region; In step S260, a second ultrasonic wave that tracks the second shear wave is emitted to the target tissue, and the second ultrasonic echo returned by the target tissue is received to obtain the second ultrasonic echo data of the target sub-tissue; wherein, the penetrating power of the second ultrasonic wave to the target sub-tissue is greater than the penetrating power of the first ultrasonic wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than the penetrating power of the first shear wave to the target sub-tissue; In step S270, a second elasticity image of the target sub-tissue is generated based on the second ultrasound echo data; In step S280, the second elastic image is output.

[0036] The elastic imaging method 200 of this application performs a second high-penetration elastic imaging on the target area in the first elastic imaging after performing elastic imaging to generate a first elastic image, thereby solving the problem that the first elastic image is incomplete or of poor quality due to insufficient penetration.

[0037] In steps S210 to S230, a first elastography process is performed. Based on conventional elastography parameters, elastography is conducted on the target tissue of the object under test to generate a first elastography image. The object under test can be a human, or an animal, such as a cat, dog, or rabbit. The target area may include, for example, a lesion area of ​​the tissue. The penetrating power of the first pushing pulse and the first ultrasound wave in this first elastography image is relatively weak. In areas with excessive depth or high hardness, such as lesion areas, inaccurate measurements or voids may occur. Figure 3A , Figure 3B As shown, where Figure 3A The image shows a first elastogram showing an underestimation due to inaccurate measurements at the lesion center. Figure 3B The image shows the first elasticity pattern, which is caused by incomplete measurements resulting in voids.

[0038] For example, before generating the first elasticity image, a tissue structure image is first generated, and the region of interest for the first elasticity image is determined based on the tissue structure image. The tissue structure image includes B-images, C-images, etc. Combined with... Figure 1The transmitting circuit 112 sends an electrical signal with an appropriate delay to each transducer element in the ultrasonic probe 110. The transducer converts the electrical signal into a first ultrasonic wave and transmits it to the tissue under test. The transducer in the ultrasonic probe 110 receives the ultrasonic echo returned by the tissue under test and converts it into an electrical signal to obtain an ultrasonic echo signal. After signal amplification, analog-to-digital conversion and other processing, the signal is transmitted to the beamforming circuit 122 for beamforming processing. Then, the beamformed ultrasonic echo signal is sent to the processor 116. The processor 116 performs logarithmic compression, dynamic range adjustment and digital scan transformation on the ultrasonic echo signal to form a tissue structure image that reflects the tissue structure of the tissue under test. The tissue structure image is then output to the display 118 for display. The user can observe the tissue structure image in real time and adjust the examination range, the angle of the ultrasonic probe 110, etc. as needed.

[0039] Next, the region of interest (ROI) is determined based on the tissue structure image to generate the first elastic image. This can be achieved by the user manually selecting the ROI bounding box and determining its location based on received user input. Alternatively, the location of the ROI can be automatically determined on the tissue structure image using relevant machine learning algorithms, i.e., the ROI bounding box is automatically generated. In other examples, the ROI can also be obtained through semi-automatic detection.

[0040] Subsequently, the processor 116 performs a first elastic imaging of the target tissue corresponding to the region of interest. In the first elastic imaging stage, a first push pulse is first emitted by the ultrasound probe 110 to generate a shear wave propagating within the target tissue of the object being measured. Then, the transmitting circuit 112 excites the ultrasound probe 110 to emit a first ultrasonic wave tracking the first shear wave towards the determined region of interest and receives the echo of the first ultrasonic wave to obtain first ultrasonic echo data. The processor 116 calculates the elastic parameter distribution based on the first ultrasonic echo data, such as shear wave velocity distribution, shear modulus distribution, Young's modulus distribution, or tissue viscosity distribution. Then, a first elastic image is generated based on the elastic parameter distribution. In the first elastic image, the elastic parameter distribution can be identified by different colors, grayscale levels, or fill methods.

[0041] For example, the elastic parameters can be calculated as follows: The displacement of a point on the propagation path of the first shear wave is calculated based on the received first ultrasonic echo data. When the displacement at that point is maximum, it is considered that the first shear wave has reached that point. The propagation path or trajectory of the first shear wave can be located by the arrival time of the first shear wave at each point, thus allowing the plotting of the shear wave trajectory. The slope of each point on the propagation path of the first shear wave can be obtained from the trajectory line, and the slope is the shear wave velocity. Based on the relationship between the shear wave velocity and Young's modulus and shear modulus, other elastic parameters, such as Young's modulus and shear modulus, can be further calculated after obtaining the shear wave velocity.

[0042] Then, the processor 116 can merge the first elastic image and the corresponding tissue structure image into a single frame. For example, the tissue structure image corresponding to the first elastic image can be either a tissue structure image generated before the first elastic imaging process to determine the region of interest, or a tissue structure image generated during the generation of the first elastic image. The processor 116 can then output the synthesized image data to the display 118 for display on the display interface of the display 118.

[0043] Next, in step S240, a target region that meets preset conditions is determined in the first elastic image. The target region is the area where the imaging effect is poor due to insufficient penetration of the first pushing pulse or the first ultrasonic wave during the first elastic imaging process. For example, the target region can be the aforementioned hollow region or the region with inaccurate measurement.

[0044] In one embodiment, the target region can be determined based on a first elastic image. See specifically... Figure 4 It can identify void regions in the first elastic image. If the area of ​​the void region is greater than a preset threshold, the void region is determined as the target region. The void region is the region that the first shear wave failed to penetrate, the region that the first ultrasonic wave failed to penetrate, or the region with a signal-to-noise ratio lower than the preset threshold. The region that the first shear wave failed to penetrate or the region that the first ultrasonic wave failed to penetrate is a void region formed because the elastic parameter could not be measured, while the region with a low signal-to-noise ratio is a void region formed because the elastic parameter could not be detected correctly.

[0045] In another embodiment, the reliability of the first elastic image can be obtained, and the target region can be determined based on the reliability of the first elastic image. The reliability of the first elastic image includes the reliability of the elastic parameters of each particle in the first elastic image. The reliability of the elastic parameters may be affected by various factors, such as the shear wave amplitude being too small or not generated, the shear wave being unable to propagate, or the signal-to-noise ratio of the first ultrasonic echo data being too low. The root cause of these issues is all related to insufficient penetration.

[0046] For example, the confidence level of the first elastic image can be calculated based on the first ultrasonic echo data described above. The processor 116 acquires the first ultrasonic echo data corresponding to each position within the first elastic image, calculates a flag value for each position to characterize the degree of interference affecting that position based on the first ultrasonic echo data, and obtains the confidence level of each position based on the flag value of each position.

[0047] The processor 116 can calculate a flag value for each location based on the acceleration curves at each location. This flag value characterizes the degree to which the location is affected by disturbance. For example, the flag value characterizing the degree of disturbance at a location is the amplitude of the acceleration curve at that location. The amplitude of the acceleration curve is either the maximum value of the acceleration curve or the maximum absolute value of the acceleration curve's amplitude. A larger amplitude of the acceleration curve indicates greater shear stress, and therefore, a smaller degree of disturbance impact. Thus, the amplitude of the acceleration curve can characterize the degree of disturbance at that location. For instance, the amplitude of the acceleration curve at each location can be directly used as the confidence level at that location, or the amplitude can be further calculated to obtain the confidence level.

[0048] The acceleration curve can be generated as follows: by comparing the differences in the first ultrasonic echo data of each position at different times, the displacement of each position at different times can be obtained to generate a displacement curve; the vibration velocity of each position at different times is calculated based on the displacement of each position at different times to generate a velocity curve; based on the vibration velocity of each position at different times, the time gradient of the velocity is calculated to obtain the acceleration of each position at different times, and finally the acceleration curve of each position is obtained.

[0049] Based on the confidence level at each location, a confidence distribution map corresponding to the first elastic image can be obtained. Different colors or grayscale values ​​can represent different levels of confidence in the confidence distribution map. For example... Figure 5 As shown, the first elasticity image and the confidence distribution map can be displayed simultaneously on the display interface to facilitate the determination of the target region in the first elasticity image based on the confidence distribution map. Alternatively, the processor 116 may not generate a confidence distribution map and may directly determine the target region in the first elasticity image based on the confidence information.

[0050] Optionally, determining the target region in the first elastic image based on confidence level may include: defining regions with confidence levels below a first preset threshold as target regions; that is, if a region has a very low confidence level, it is designated as a target region. Alternatively, a single region with a confidence level below a second preset threshold and an area exceeding a preset area may be defined as a target region, where the second preset threshold may be lower than the first preset threshold. In other words, if a region with low confidence level has an excessively large area, it is designated as a target region.

[0051] In other embodiments, the target region can also be determined based on a tissue structure image corresponding to the first elastic image. For example, such as... Figure 6 As shown, because the lesion tissue has high hardness and large area, the first shear wave has difficulty penetrating it. Therefore, the lesion area can be identified in the tissue structure image corresponding to the first elastic image, and the area corresponding to the lesion area in the first elastic image can be used as the target area.

[0052] Whether the target region is determined based on the first elastic image, the confidence level of the first elastic image, or the tissue structure image corresponding to the first elastic image, it can be automatically determined by the processor 116 or manually determined by the user. When automatically determined by the processor 116, the processor can automatically draw the target region according to a preset shape or size when the above-mentioned determination conditions are met. When the target region is determined manually, the processor receives a user instruction to select the target region and determines the target region according to the received user instruction. The size and shape of the target region can be diverse, such as rectangle, circle, convex, fan shape, etc., or an irregular shape obtained by tracing image information, such as the shape obtained by tracing a region with a confidence level lower than a first preset threshold, or the shape obtained by tracing a lesion region in the tissue structure image corresponding to the first elastic image.

[0053] After determining the target area, in steps S250 to S270, a second elastic imaging process is performed based on the target area to achieve high-penetration elastic imaging.

[0054] Since the first and second elastography are performed sequentially, to ensure the stability of the scanning section as much as possible, a tissue structure image of the target tissue can be generated and displayed in real time before the second elastography, i.e., before the second push pulse is emitted. The real-time generated tissue structure image guides the user to adjust the ultrasound probe 110 to find the scanning section corresponding to the first elastography image. Specifically, the transmitting circuit 112 excites the ultrasound probe 110 to emit ultrasound waves towards the target tissue; the receiving circuit receives the ultrasound echo returned from the target tissue and converts it into an electrical signal to obtain ultrasound echo data; the processor 116 performs logarithmic compression, dynamic range adjustment, and digital scan transformation on the ultrasound echo data to form a tissue structure image that reflects the tissue structure of the tissue under test, and outputs the tissue structure image to the display 118 for real-time display.

[0055] Furthermore, the matching degree between the tissue structure image of the target tissue and the corresponding tissue structure image of the first elastic image can be determined in real time and displayed in real time. A high matching degree indicates a high consistency between the scanning section of the current ultrasound probe and the section of the first elastic image. In one example, the matching degree of the images can be determined by feature extraction. Specifically, the first image features of the tissue structure image corresponding to the first elastic image are extracted in advance, and the second image features of the currently acquired tissue structure image are extracted in real time. The first image features and the second image features are compared in real time to obtain the matching degree between the two. Traditional feature extraction algorithms such as gradient feature extraction, Haar feature extraction, and texture feature extraction can be used, or deep neural networks can be used for feature extraction.

[0056] In another example, a machine learning model can be used to determine the matching degree between the tissue structure image corresponding to the first elastic image and the currently acquired tissue structure image in real time. The machine learning model can be a trained deep learning neural network model that can be trained to directly output the matching degree between the two input images.

[0057] With the help of real-time displayed tissue structure images and matching prompts, the user places the ultrasound probe 110 in a suitable position and angle and keeps it stable before triggering the second elastography. The second elastography includes the emission of a second push pulse, the emission of a second ultrasound wave, and the reception of a second ultrasound echo. The second push pulse generates a second shear wave that propagates within the target sub-tissue corresponding to the target region, and the second ultrasound wave is used to detect tissue motion information caused by the second shear wave.

[0058] The target sub-tissue is the portion of tissue corresponding to the target region, that is, the portion of tissue that the first shear wave or the first ultrasound failed to penetrate during the first elastography. The target sub-tissue generally has high hardness, and may be, for example, lesion tissue. Increasing the penetrating power of the second shear wave or the second ultrasound helps to achieve high-penetration elastography. Therefore, in the elastography method 200 of this application embodiment, the penetrating power of the second ultrasound to the target sub-tissue is greater than that of the first ultrasound, or the penetrating power of the second shear wave to the target sub-tissue is greater than that of the first shear wave to the target sub-tissue, or the penetrating power of the second ultrasound to the target sub-tissue is greater than that of the first ultrasound to the target sub-tissue, and the penetrating power of the second shear wave to the target sub-tissue is greater than that of the first shear wave to the target sub-tissue.

[0059] In step S250, a second pushing pulse is emitted towards the target tissue to generate a second shear wave that propagates within the target sub-tissue corresponding to the target region. The penetrating power of the second shear wave into the target sub-tissue is greater than that of the first shear wave, and this can be achieved in ways including but not limited to the following: As one implementation method, since the target area is generally smaller than the original region of interest, and the range of the target sub-organism is smaller than the range of the target organization, the second driving pulse only needs to ensure that the second shear wave covers the new target sub-organism. Therefore, the acoustic field focusing intensity of the second driving pulse can be more concentrated. A more concentrated acoustic field focusing intensity can increase the amplitude of the generated second shear wave, allowing it to propagate further, resulting in a stronger detected signal and better resistance to noise interference, thereby improving the penetration power of the second shear wave. Penetration power includes penetration distance or penetration depth.

[0060] To make the focusing intensity of the second driving pulse higher than that of the first driving pulse, in one embodiment, such as Figure 7 As shown, the delay of each element within the emission aperture of the ultrasonic probe can be adjusted based on the target area to adjust the acoustic field shape of the second driving pulse, so that the focusing intensity of the second driving pulse is higher than that of the first driving pulse.

[0061] In another embodiment, such as Figure 8 As shown, at least one of the focal point position and the number of focal points of the second push pulse can be adjusted based on the target area, thereby making the focal intensity of the second push pulse higher than that of the first push pulse.

[0062] Both of these methods can make the focusing intensity of the second driving pulse stronger, thereby improving the penetration of the second shear wave.

[0063] As another implementation method, since shear waves attenuate rapidly and propagate over short distances within hard tissues, to enhance the penetrating power of the second shear wave, second driving pulses can be emitted at at least two locations near the target sub-tissue, thereby generating shear wave sources at at least two locations near the target sub-tissue. For example, Figure 9 As shown, second push pulses can be emitted from the left, center, and right sides of the target sub-tissue to generate second shear waves. The number and interval of the emitted second push pulses can be preset. For each second shear wave, a second ultrasonic wave tracking the second shear wave is emitted to obtain at least two sets of second ultrasonic echo data corresponding to at least two second shear waves, thereby detecting relevant information about the propagation of each second shear wave.

[0064] When second push pulses are generated at two locations, at least two sets of elastic parameters of the target tissue are obtained based on at least two sets of second ultrasound echo data. A final elastic parameter is then obtained based on these at least two sets of elastic parameters, and a second elastic image is generated based on the final elastic parameter. The final elastic parameter can be obtained from the at least two sets of elastic parameters in at least one of the following ways: First, the final elastic parameter is obtained by splicing the at least two sets of elastic parameters. This allows for the acquisition of a complete result if the propagation distance of the second shear wave is insufficient, by splicing the detection results of the second shear wave at multiple locations. Second, the final elastic parameter is obtained by averaging the at least two sets of elastic parameters. This distributes the error in the elastic parameters and improves the accuracy of the measurement results. Third, the final elastic parameter is obtained by selecting the at least one set of elastic parameters with the highest reliability from the at least two sets of elastic parameters. This allows for the acquisition of a reliable result if the second shear wave source at a particular location is poor or the propagation is not ideal, as second shear waves from other locations can be used as substitutes.

[0065] Furthermore, emitting the second push pulse at at least two locations near the target sub-tissue based on the target region includes emitting the second push pulse sequentially at said at least two locations. Due to safety limitations of ultrasound probes, emitting the second push pulse simultaneously at multiple locations may reduce the intensity of a single second push pulse, which is detrimental to improving the penetration of the second shear wave. Emitting the second push pulse sequentially avoids this problem.

[0066] In step S260, a second ultrasonic wave tracking the second shear wave is emitted towards the target tissue, and the second ultrasonic echo returned by the target tissue is received to obtain the second ultrasonic echo data of the target sub-tissue. Optionally, in order to completely record the propagation process of the second shear wave within the target tissue, the second ultrasonic wave generally needs to be emitted continuously for a period of time.

[0067] In this embodiment, since the target sub-tissue is relatively small, the detection range of the second ultrasound can be sufficiently reduced. The sound field range of the second ultrasound only needs to cover the target sub-tissue. Figure 10 As shown, a stronger focusing method can be used to enhance the acoustic energy of the second ultrasound wave, thereby increasing the signal-to-noise ratio of the second ultrasound echo data.

[0068] In another embodiment, to improve the penetrating power of the second ultrasound wave, its emission frequency can be controlled to be lower than that of the first ultrasound wave. Lower frequency ultrasound waves consume less energy to propagate through tissue, resulting in stronger penetrating power. Furthermore, when the emission frequency is lower, the waveform length of the second ultrasound wave is longer, thus providing stronger anti-interference capabilities.

[0069] In one embodiment, since the depth of small target sub-tissues is generally shallower than the depth of the target tissue, the interval between the emission of the second ultrasound wave and the reception of its echo is shorter, and the emission interval between two adjacent second ultrasound waves can also be shorter. Therefore, the emission interval of the second ultrasound wave can be controlled to be less than the emission interval of the first ultrasound wave to improve the detection rate. Shear wave propagation speed in high-hardness tissues is often very fast. For shear wave propagation over a fixed distance, it means that the shear wave arrives at two locations very close together. If the detection rate is insufficient, the interval time cannot be accurately distinguished, and thus the propagation speed of the shear wave cannot be accurately calculated. Therefore, improving the detection rate helps to improve the accuracy of elastic parameter calculation and avoids underestimation of elastic parameters or the appearance of voids in the elasticity image.

[0070] In another embodiment, the emission voltage of the second ultrasonic wave can be controlled to be higher than that of the first ultrasonic wave. A higher emission voltage results in stronger penetration.

[0071] It is worth noting that in conventional elastography, to simultaneously observe tissue structure images, it is often necessary to simultaneously transmit and receive imaging sequences of tissue structure images, such as B-image sequences or C-image sequences. Therefore, conventional elastography can simultaneously acquire tissue structure images and elasticity images; for example, while acquiring the first elasticity image, the corresponding tissue structure image can also be acquired. To achieve real-time observation, the transmission frequency of the ultrasound waves used to generate tissue structure images is usually relatively high, thus limiting the energy of the ultrasound waves used to generate elasticity images.

[0072] In this embodiment, only the second elastic image needs to be generated during the second elastic imaging process, and no tissue structure image needs to be generated. Therefore, it is not necessary to emit ultrasound waves for generating tissue structure images. Only ultrasound waves for generating the second elastic image need to be emitted, namely the second push pulse and the second ultrasound waves. This ensures that the energy of the second push pulse and the second ultrasound waves is no longer affected by other emissions, and the emission voltage can be increased as much as possible within a safe range, thereby further improving the penetration of the second shear wave and the second ultrasound waves.

[0073] In step S270, a second elastic image of the target sub-tissue is generated based on the second ultrasonic echo data. Generating the second elastic image based on the second ultrasonic echo data is similar to generating the first elastic image based on the first ultrasonic echo data described above. Specifically, the displacement of a point on the propagation path of the second shear wave is calculated based on the second ultrasonic echo signal. The propagation path or trajectory of the second shear wave can be located by the arrival time of the second shear wave at each point, thus allowing the drawing of a shear wave trajectory diagram. The slope of each point on the propagation path of the second shear wave can be obtained from the trajectory line, and the slope is the shear wave velocity. Based on the relationship between the shear wave velocity and Young's modulus and shear modulus, other elastic parameters, such as Young's modulus and shear modulus, can be further calculated after obtaining the shear wave velocity. Then, the distribution of elastic parameters at various locations within the target area is represented using different gray levels and colors, thus obtaining the second elastic image.

[0074] In step S280, one way to output the second elastic image may include: replacing a portion of the first elastic image located within the target region with the second elastic image, such as... Figure 11 As shown. Specifically, after calculating the elastic parameters at various locations in the target region based on the second ultrasound echo data, since these elastic parameters are more accurate than those obtained during the first elastic imaging process, they can directly replace the elastic parameters obtained during the first elastic imaging process for the target region, and be displayed within the target region of the first elastic image in a way such as color coding. The color coding pattern can be different from or the same as the first elastic image.

[0075] Another way to output the second elastic image may be to overlay the second elastic image onto the target area of ​​the first elastic image. For example, during the overlay display, a certain degree of transparency can be set for the second elastic image to facilitate comparison and observation between the second and first elastic images by the user.

[0076] In addition to the two methods mentioned above, a second elastic image can also be displayed separately in an area other than the first elastic image, either simultaneously with or switched between the first elastic image, to facilitate comparison and observation by the user.

[0077] The above exemplarily illustrates an elastic imaging method 200 according to an embodiment of this application. Based on the above description, the elastic imaging method 200 according to the embodiment of this application performs high-penetration elastic imaging on the target area in the first elastic image after generating a conventional first elastic image, thus solving problems such as voids and inaccurate measurements caused by insufficient penetration during elastic imaging.

[0078] This application also provides an ultrasound imaging system for implementing the above-described elastic imaging method 200. The ultrasound imaging system includes an ultrasound probe, a transmitting circuit, a receiving circuit, a processor, and a display. Now referring back to... Figure 1 This ultrasound imaging system can achieve the following: Figure 1 The ultrasound imaging system 100 is shown. As described above, the ultrasound imaging system 100 may include an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116, and a display 118. The transmitting circuit 112 is used to excite the ultrasound probe 110 to emit a push pulse towards the target tissue of the object being measured, thereby generating a shear wave propagating within the target tissue. The transmitting circuit 112 is also used to excite the ultrasound probe 110 to emit ultrasound waves that track the shear wave towards the target tissue. The receiving circuit controls the ultrasound probe 110 to receive the ultrasound echo returned from the target tissue to obtain ultrasound echo data. The processor is used to execute the steps of the elastography method 200. The display 112 is used to output the elastography image obtained by the processor. The ultrasound imaging system may also include a transmit / receive selection switch 120 and a beamforming module 122; the relevant descriptions of the various components can be found above.

[0079] Specifically, when implementing the elastic imaging method 200, the transmitting circuit 112 is used to excite the ultrasound probe 110 to transmit a first push pulse toward the target tissue of the object being measured, so as to generate a first shear wave propagating within the target tissue; and to excite the ultrasound probe 110 to transmit a first ultrasonic wave that tracks the first shear wave toward the target tissue; the receiving circuit 114 is used to control the ultrasound probe 110 to receive the first ultrasonic echo returned by the target tissue, so as to obtain the first ultrasonic echo data.

[0080] The processor 116 is used to generate a first elastic image of the target tissue based on the first ultrasound echo data, and to determine a target region in the first elastic image that meets preset conditions.

[0081] The transmitting circuit 112 is also used to excite the ultrasound probe 110 to transmit a second push pulse to the target tissue based on the target region, so as to generate a second shear wave propagating in the target sub-tissue corresponding to the target region; and to excite the ultrasound probe 110 to transmit a second ultrasound wave that tracks the second shear wave to the target tissue.

[0082] The receiving circuit 114 is also used to receive the second ultrasonic echo returned by the target tissue to obtain the second ultrasonic echo data of the target sub-tissue; wherein the penetrating power of the second ultrasonic wave to the target sub-tissue is greater than that of the first ultrasonic wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than that of the first shear wave to the target sub-tissue.

[0083] Processor 116 is also used to generate a second elastic image of the target sub-tissue based on the second ultrasound echo data.

[0084] Display 118 is used to output a second elastic image.

[0085] The above only describes the main functions of each component of the ultrasound imaging system 100. For more details, please refer to the relevant description of the elastic imaging method 200. After generating a conventional first elastic image, the ultrasound imaging system of this application performs high-penetration elastic imaging on the target area in the first elastic image, solving problems such as voids and inaccurate measurements caused by insufficient penetration during elastic imaging.

[0086] The following is a reference to the appendix. Figure 12 A method for elastic imaging according to another embodiment of this application is described. Figure 12 A schematic flowchart of an elastic imaging method 1200 according to another embodiment of this application is shown. Figure 12 As shown, the elastic imaging method 1200 of this application embodiment includes the following steps: Step S1210: Obtain a first elastic image and a first tissue structure image of the target tissue of the test object. The first elastic image and the first tissue structure image correspond to the same tissue cross-section. The first elastic image is obtained by detecting a first ultrasonic wave of a first shear wave propagating in the target tissue and based on a first ultrasonic echo of the first ultrasonic wave. Step S1220: Determine a target region that meets preset conditions in the first elastic image or the first tissue structure image; Step S1230: Based on the target region, a push pulse is emitted toward the target tissue to generate a second shear wave propagating within the target sub-tissue corresponding to the target region; Step S1240: A second ultrasonic wave that tracks the second shear wave is emitted to the target tissue, and the second ultrasonic echo returned by the target tissue is received to obtain the second ultrasonic echo data of the target sub-tissue; wherein, the penetrating power of the second ultrasonic wave to the target sub-tissue is greater than the penetrating power of the first ultrasonic wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than the penetrating power of the first shear wave to the target sub-tissue; Step S1250: Obtain a second elastic image of the target sub-tissue based on the second ultrasound echo data; Step S1260: Output the second elastic image.

[0087] The difference between the elastography method 1200 of this application embodiment and the elastography method 200 described above is that, in step S1210 of the elastography method 1200, not only is a first elastic image acquired, but also a first tissue structure image that maintains the same tissue cross-section as the first elastic image is acquired. Furthermore, the first elastic image and the first tissue structure image are not limited to real-time acquisition, but can be pre-acquired images extracted from a storage medium or received via remote transmission. Specific details regarding the generation of the first elastic image and the first tissue structure image can be found in steps S210 to S230 of the elastography method 200, where the first tissue structure image is the tissue structure image corresponding to the first elastic image generated during the first elastography process described above.

[0088] Subsequently, in step S1220, a target region satisfying preset conditions is determined in the first elastic image or the first tissue structure image. Determining the target region in the first elastic image may include: identifying void regions in the first elastic image; if the area of ​​a void region is greater than a preset threshold, then the void region is determined as the target region. The void region is an area that the first shear wave failed to penetrate, an area that the first ultrasound wave failed to penetrate, or an area with a signal-to-noise ratio lower than a preset threshold. Alternatively, determining the target region in the first elastic image may include: obtaining the confidence level of the first elastic image and determining the target region based on the confidence level. Determining the target region in the first tissue structure may include: identifying lesion regions in the tissue structure image and determining the lesion regions as the target regions.

[0089] After determining the target region, the elastography method 1200 may further include: generating and displaying a second tissue structure image of the target tissue in real time to guide the emission of a driving pulse based on the second tissue structure image. Since the first and second elastography images are generated sequentially, the second tissue structure image can assist the user in finding the same tissue section corresponding to the first elastography image to generate the second elastography image. For example, while displaying the second tissue structure image, the matching degree between the second and first tissue structure images can also be determined and displayed in real time, so that the user can refer to the matching degree to find the same tissue section corresponding to the first elastography image and perform high-penetration elastography. Specific details of high-penetration elastography can be found in steps S250 to S270 of the elastography method 200.

[0090] Optionally, after generating the second elastic image, in step S1260, the method of outputting the second elastic image includes at least one of the following: replacing the portion of the first elastic image located within the target area with the second elastic image; superimposing the second elastic image on the target area in the first elastic image; or displaying the second elastic image separately in the area outside the first elastic image.

[0091] In addition, the elastic imaging method 1200 of this application embodiment has many similar or identical contents to the elastic imaging method 200 described above, which can be referred to above for details, and will not be repeated here.

[0092] The above exemplarily illustrates an elastic imaging method 1200 according to an embodiment of this application. Based on the above description, the elastic imaging method 1200 according to the embodiment of this application, after acquiring a first elastic image and a first tissue structure image, performs high-penetration elastic imaging on a target area in the first elastic image or the first tissue structure image, solving problems such as voids and inaccurate measurements caused by insufficient penetration during elastic imaging.

[0093] This application also provides an ultrasound imaging system for implementing the above-described elastic imaging method 1200. The ultrasound imaging system includes an ultrasound probe, a transmitting circuit, a receiving circuit, a processor, and a display. Now, referring back to... Figure 1 This ultrasound imaging system can achieve the following: Figure 1 The ultrasound imaging system 100 is shown. As described above, the ultrasound imaging system 100 may include an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116, and a display 118. The transmitting circuit 112 is used to excite the ultrasound probe 110 to emit a push pulse towards the target tissue of the object being measured, thereby generating a shear wave propagating within the target tissue. The transmitting circuit 112 is also used to excite the ultrasound probe 110 to emit ultrasound waves that track the shear wave towards the target tissue. The receiving circuit controls the ultrasound probe 110 to receive the ultrasound echo returned from the target tissue to obtain ultrasound echo data. The processor is used to execute the steps of the elastography method 1200. The display 112 is used to output the elastography image obtained by the processor. The ultrasound imaging system may also include a transmit / receive selection switch 120 and a beamforming module 122; the relevant descriptions of the various components can be found above.

[0094] Specifically, when implementing the elastic imaging method 1200, the processor 116 is used to: acquire a first elastic image and a first tissue structure image of the target tissue of the object under test, wherein the first elastic image and the first tissue structure image correspond to the same tissue cross section, and the first elastic image is obtained by detecting a first ultrasonic wave of a first shear wave propagating in the target tissue and based on a first ultrasonic echo of the first ultrasonic wave; the processor 116 is also used to determine a target region that meets preset conditions in the first elastic image or the first tissue structure image.

[0095] The transmitting circuit 112 is used to excite the ultrasound probe 110 to emit a push pulse toward the target tissue based on the target region, so as to generate a second shear wave propagating in the target sub-tissue corresponding to the target region; and to excite the ultrasound probe 110 to emit a second ultrasound wave that tracks the second shear wave toward the target tissue.

[0096] The receiving circuit 114 is used to control the ultrasound probe 110 to receive the second ultrasound echo returned by the target tissue to obtain the second ultrasound echo data; wherein the penetrating power of the second ultrasound wave to the target sub-tissue is greater than the penetrating power of the first ultrasound wave to the target sub-tissue, and / or the penetrating power of the second shear wave to the target sub-tissue is greater than the penetrating power of the first shear wave to the target sub-tissue.

[0097] The processor 116 is also used to obtain a second elastic image of the target sub-tissue based on the second ultrasound echo data. The display 118 is used to output the second elastic image.

[0098] The above only describes the main functions of each component of the ultrasound imaging system 100. For more details, please refer to the relevant description of the elastic imaging method 1200. After acquiring the first elastic image and the first tissue structure image, the ultrasound imaging system of this application performs high-penetration elastic imaging on the target area in the first elastic image or the first tissue structure image, which solves the problems of voids and inaccurate measurements caused by insufficient penetration in the elastic imaging process.

[0099] The following is a reference to the appendix. Figure 13 A method for elastic imaging according to another embodiment of this application is described. Figure 13 A schematic flowchart of an elastic imaging method 1300 according to another embodiment of this application is shown. Figure 13 As shown, the elastic imaging method 1300 of this application embodiment includes the following steps: Step S1310: Provide an option for at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponds to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponds to a second push pulse and a second ultrasound. Step S1320: When a selection instruction for the second elastic imaging mode is received, a second push pulse is emitted toward the target tissue of the object under test to generate a second shear wave propagating within the target tissue. Step S1330: A second ultrasonic wave that tracks the second shear wave is emitted to the target tissue, and the ultrasonic echo returned by the target tissue is received to obtain ultrasonic echo data; wherein, the penetrating power of the second ultrasonic wave to the target tissue is greater than the penetrating power of the first ultrasonic wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first driving pulse to the target tissue; Step S1340: Obtain a second elastic image of the target tissue based on the ultrasound echo data; Step S1350: Output the second elastic image.

[0100] The elastography method 1300 of this application embodiment is mainly used to provide elastography modes with different penetration powers for target tissues. The second elastography mode is used for high-penetration elastography of the target tissue, solving the problem that conventional elastography cannot effectively penetrate the target tissue. For example, in step S1310, the option to provide at least two elastography modes may include providing at least two elastography modes on the display interface of the ultrasound imaging system. Each elastography mode corresponds to a push pulse and an ultrasound wave. The option for at least two elastography modes may be an icon option or a menu bar option, etc. The first elastography mode is a conventional elastography mode, and its imaging method can refer to the first elastography in elastography method 200. The second elastography mode is a high-penetration elastography mode, and its imaging method is similar to the second elastography in elastography method 200. The penetrating power of the second shear wave generated by the second push pulse in the target tissue under the second elastography mode is greater than the penetrating power of the first shear wave generated by the first push pulse in the target tissue under the first elastography mode, or the penetrating power of the second ultrasound wave in the target tissue under the second elastography mode is greater than the penetrating power of the first ultrasound wave in the target tissue under the first elastography mode.

[0101] Optionally, in addition to displaying at least two elastic imaging modes on the display interface, the option of at least two elastic imaging modes can also be provided through other human-computer interaction devices, such as controlling the selection of elastic imaging modes via a knob, or controlling whether to enable the second elastic imaging mode via a power switch. Alternatively, after performing the first elastic imaging using the first elastic imaging mode, the system can automatically determine whether to enable the second elastic imaging mode for high-penetration elastic imaging based on the results of the first elastic imaging.

[0102] In some embodiments, a first elastic image of the target tissue can be generated first in a first elastic imaging mode, and a second elastic imaging mode can be entered when a target region satisfying preset conditions exists in the first elastic image. Specifically, the following steps are performed in the first elastic imaging mode: a first push pulse is emitted to the target tissue of the object under test to generate a first shear wave propagating within the target tissue; a first ultrasonic wave tracking the first shear wave is emitted to the target tissue, the ultrasonic echo returned by the target tissue is received, and a first elastic image is generated; a target region satisfying preset conditions is determined in the first elastic image, such that a second push pulse is emitted to the target tissue based on the target region. The target region satisfying the preset conditions can be determined based on the first elastic image or based on a tissue structure image corresponding to the first elastic image.

[0103] For example, in addition to identifying hollow areas, confidence level, or manual user confirmation (see the relevant description of step S240 for details, which will not be repeated here), the target area meeting the preset conditions may also include at least one of the following: the tissue type contained in the target area, the boundary morphology of the lesions contained in the target area, the area size of the lesions contained in the target area, the grayscale of the target area, and the brightness of the target area. Specifically, regarding the tissue type contained in the target area, some tissue types have higher hardness, such as breast tissue, so the second elastography mode can be entered when the target area contains a preset tissue type. Regarding the boundary morphology of the lesions contained in the target area, harder tissues tend to have more irregular morphologies, so the second elastography mode can be entered when the boundary of the lesions in the target area has a preset morphology. Regarding the area size of the lesions contained in the target area, the larger the lesion area, the higher its hardness, and the more difficult it is for shear waves and ultrasound waves to penetrate. Therefore, the area size of the lesions contained in the target area can be determined. If the area of ​​the lesions contained in the target area exceeds a preset threshold, the second elastography mode is entered. Regarding the grayscale and brightness of the target area, generally, the lower the grayscale and brightness, the greater the hardness, and the more difficult it is for shear waves and ultrasonic waves to penetrate. Therefore, the second elastic imaging mode can be entered when the grayscale or brightness of the target area is below a preset threshold. It should be noted that in the specific implementation, the system can determine whether the target area meets the preset conditions, and if so, the system automatically enters the second elastic imaging mode. Alternatively, the user can determine whether the target area meets the preset conditions, and if so, manually enter the second elastic imaging mode. The specific method of manual operation can be icon selection, power button selection, button selection, or knob selection, etc., without specific limitations here.

[0104] To make the penetrating power of the second shear wave greater than that of the first shear wave in the target tissue, in some embodiments, the acoustic field morphology of the second driving pulse can be adjusted by regulating the delay of each element within the emission aperture of the ultrasonic probe, thereby making the focusing intensity of the second driving pulse higher than that of the first driving pulse, thus making the penetrating power of the second shear wave greater than that of the first shear wave. In other embodiments, the focusing point position and number of the second driving pulse can be adjusted to make the focusing intensity of the second driving pulse higher than that of the first driving pulse, thereby making the penetrating power of the second shear wave greater than that of the first shear wave.

[0105] Alternatively, second push pulses can be emitted sequentially at at least two locations near the target tissue, such that the penetrating power of the second shear wave is greater than that of the first shear wave. Accordingly, emitting ultrasound waves tracking the second shear waves towards the target tissue includes: emitting ultrasound waves tracking each of the second shear waves to obtain at least two sets of ultrasound echo data corresponding to at least two second push pulses; obtaining an elastic image of the target tissue based on the ultrasound echo data includes obtaining the elastic image based on at least two sets of ultrasound echo data.

[0106] If the penetrating power of the second ultrasonic wave is to be greater than that of the first ultrasonic wave, in some embodiments, the emission interval of the second ultrasonic wave can be smaller than that of the first ultrasonic wave, the emission frequency of the second ultrasonic wave can be smaller than that of the first ultrasonic wave, or the emission voltage of the second ultrasonic wave can be greater than that of the first ultrasonic wave, thereby making the penetrating power of the second ultrasonic wave greater than that of the first ultrasonic wave.

[0107] The above exemplarily illustrates an elastic imaging method 1300 according to an embodiment of this application. Based on the above description, the elastic imaging method 1300 according to the embodiment of this application can achieve high-penetration elastic imaging, solving problems such as voids and inaccurate measurements caused by insufficient penetration during elastic imaging.

[0108] This application also provides an ultrasound imaging system for implementing the above-described elastic imaging method 1300. The ultrasound imaging system includes an ultrasound probe, a transmitting circuit, a receiving circuit, a processor, and a human-machine interface device, which includes a display. Now referring back to... Figure 1 This ultrasound imaging system can achieve the following: Figure 1 The ultrasound imaging system 100 is shown. As described above, the ultrasound imaging system 100 may include an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116, and a display 118. The transmitting circuit 112 is used to excite the ultrasound probe 110 to emit a push pulse towards the target tissue of the object being measured, thereby generating a shear wave propagating within the target tissue. The transmitting circuit 112 is also used to excite the ultrasound probe 110 to emit ultrasound waves that track the shear wave towards the target tissue. The receiving circuit controls the ultrasound probe 110 to receive the ultrasound echo returned from the target tissue to obtain ultrasound echo data. The processor is used to execute the steps of the elastography method 1300. The display 112 is used to output the elastography image obtained by the processor. The ultrasound imaging system may also include a transmit / receive selection switch 120 and a beamforming module 122; the relevant descriptions of the various components can be found above.

[0109] Specifically, when implementing the elastography method 1300, the human-computer interaction device is used to provide options for at least two elastography modes, wherein the at least two elastography modes include a first elastography mode and a second elastography mode, the first elastography mode corresponding to a first push pulse and a first ultrasound wave, and the second elastography mode corresponding to a second push pulse and a second ultrasound wave; the transmitting circuit 112 is used to, when receiving a selection instruction for the second elastography mode, excite the ultrasound probe 110 to emit a first push pulse toward the target tissue of the object being measured to generate a second shear wave propagating within the target tissue; and excite the ultrasound probe 110 to emit a second ultrasound wave that tracks the second shear wave toward the target tissue; the receiving circuit 114 is used to receive the ultrasound echo returned by the target tissue to obtain ultrasound echo data; wherein the penetrating power of the second ultrasound wave to the target tissue is greater than the penetrating power of the first ultrasound wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first push pulse to the target tissue; the processor 116 is used to obtain an elastic image of the target tissue based on the ultrasound echo data; and the display 118 is used to output the elastic image.

[0110] The above only describes the main functions of each component of the ultrasound imaging system 100. For more details, please refer to the relevant description of the elastography method 1300. The ultrasound imaging system of this application embodiment can achieve high-penetration elastography, solving problems such as voids and inaccurate measurements caused by insufficient penetration during elastography.

[0111] The following is a reference to the appendix. Figure 14 A method for elastic imaging according to another embodiment of this application is described. Figure 14 A schematic flowchart of an elastic imaging method 1400 according to another embodiment of this application is shown. Figure 14 As shown, the elastic imaging method 1400 of this application embodiment includes the following steps: In step S1410, a first ultrasound image of the target tissue of the tested object is acquired, wherein the first ultrasound image includes a tissue structure image; In step S1420, a target region that meets the preset conditions is determined in the first ultrasound image; In step S1430, at least two elastic imaging modes are provided as options, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponds to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponds to a second push pulse and a second ultrasound. In step S1440, in the second elastic imaging mode, a second push pulse is emitted toward the target tissue based on the target region to generate a second shear wave propagating within the target tissue; In step S1450, a second ultrasonic wave that tracks the second shear wave is emitted to the target tissue, and the ultrasonic echo returned by the target tissue is received to obtain ultrasonic echo data, wherein the penetrating power of the second ultrasonic wave to the target tissue is greater than the penetrating power of the first ultrasonic wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first pushing pulse to the target tissue; In step S1460, an elastic image of the target tissue is obtained based on the ultrasound echo data; In step S1470, the elastic image is output.

[0112] In the elastography method 1400 of this application embodiment, after generating a first ultrasound image, at least two elastography modes are provided as options, and high-penetration elastography is performed on the target area in the first ultrasound image in the second elastography mode to solve the problem of voids or inaccurate measurements in the elastography image due to insufficient penetration.

[0113] In one embodiment, the system can automatically enter a second elastic imaging mode when the target area meets preset conditions. These preset conditions include at least one of the following: the type of tissue contained in the target area, the boundary morphology of the lesions contained in the target area, the area size of the lesions contained in the target area, the grayscale of the target area, and the brightness of the target area. Specifically, regarding the type of tissue contained in the target area, some types of tissue have higher hardness, such as breast tissue; therefore, the system can enter the second elastic imaging mode when the target area contains a preset tissue type. Regarding the boundary morphology of the lesions contained in the target area, harder tissues tend to have more irregular morphologies; therefore, the system can enter the second elastic imaging mode when the boundary of the lesions in the target area has a preset morphology. Regarding the area size of the lesions contained in the target area, the larger the lesion area, the more difficult it is for shear waves and ultrasound waves to penetrate; therefore, the system can determine the area size of the lesions contained in the target area. If the area of ​​the lesions contained in the target area exceeds a preset threshold, the system enters the second elastic imaging mode. Regarding the grayscale and brightness of the target area, the lower the grayscale and brightness, the more difficult it is for shear waves and ultrasound waves to penetrate; therefore, the system can enter the second elastic imaging mode when the grayscale or brightness of the target area is below a preset threshold. Optionally, the first ultrasound image may also include other ultrasound images besides tissue structure images, such as elasticity images corresponding to tissue structure images.

[0114] Alternatively, the second elastography mode can be entered upon receiving a selection instruction for the second elastography mode. For example, at least two elastography mode options can be provided on the display interface of the ultrasound imaging system, each corresponding to an imaging method. The options for the at least two elastography modes can be icon options or menu bar options, etc. Specific details of the second elastography mode can be found in the second elastography in elastography method 200; specific details of the first elastography mode can be found in the first elastography in elastography method 200.

[0115] Alternatively, in addition to displaying at least two options for elastic imaging modes on the display interface, at least two options for elastic imaging modes can also be provided through other human-computer interaction devices, such as controlling the selection of elastic imaging modes with a knob, or controlling whether to enable high-penetration imaging mode with a power switch.

[0116] The above exemplarily illustrates an elastic imaging method 1400 according to an embodiment of this application. Based on the above description, the elastic imaging method 1400 according to the embodiment of this application can achieve high-penetration elastic imaging, solving problems such as voids and inaccurate measurements caused by insufficient penetration during elastic imaging.

[0117] This application also provides an ultrasound imaging system for implementing the above-described elastic imaging method 1400. The ultrasound imaging system includes an ultrasound probe, a transmitting circuit, a receiving circuit, a processor, and a human-machine interface device, which includes a display. Now referring back to... Figure 1 This ultrasound imaging system can achieve the following: Figure 1 The ultrasound imaging system 100 is shown. As described above, the ultrasound imaging system 100 may include an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116, and a display 118. The transmitting circuit 112 is used to excite the ultrasound probe 110 to emit a push pulse towards the target tissue of the object being measured, thereby generating a shear wave propagating within the target tissue. The transmitting circuit 112 is also used to excite the ultrasound probe 110 to emit ultrasound waves that track the shear wave towards the target tissue. The receiving circuit controls the ultrasound probe 110 to receive the ultrasound echo returned from the target tissue to obtain ultrasound echo data. The processor is used to execute the steps of the elastography method 1400. The display 112 is used to output the elastography image obtained by the processor. The ultrasound imaging system may also include a transmit / receive selection switch 120 and a beamforming module 122; the relevant descriptions of the various components can be found above.

[0118] Specifically, when implementing the elastography method 1400, the processor 116 is used to acquire a first ultrasound image of the target tissue of the object under test, wherein the first ultrasound image includes a tissue structure image; the processor 116 is also used to determine a target region in the first ultrasound image that meets preset conditions; the human-computer interaction device is used to provide options for at least two elastography modes, wherein the at least two elastography modes include a first elastography mode and a second elastography mode, the first elastography mode corresponds to a first push pulse and a first ultrasound wave, and the second elastography mode corresponds to a second push pulse and a second ultrasound wave; the transmitting circuit 112 is used to excite the ultrasound probe 110 to project onto the target tissue based on the target region in the second elastography mode. A second push pulse is emitted to generate a second shear wave propagating within the target tissue; and the ultrasound probe 110 is excited to emit a second ultrasound wave that tracks the second shear wave toward the target tissue; a receiving circuit 114 is used to control the ultrasound probe 110 to receive the ultrasound echo returned by the target tissue to obtain ultrasound echo data; wherein the penetrating power of the second ultrasound wave to the target tissue is greater than the penetrating power of the first ultrasound wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first push pulse to the target tissue; the processor 116 is also used to obtain an elastic image of the target tissue based on the ultrasound echo data; and a display 118 is used to output the elastic image.

[0119] The above only describes the main functions of each component of the ultrasound imaging system 100. For more details, please refer to the relevant description of the elastography method 1400. The ultrasound imaging system of this application embodiment can achieve high-penetration elastography, solving problems such as voids and inaccurate measurements caused by insufficient penetration during elastography.

[0120] Furthermore, according to embodiments of this application, a storage medium is also provided, on which program instructions are stored. When executed by a computer or processor, these program instructions are used to perform corresponding steps of the elastic imaging methods 200, 1200, 1300, or 1400 of the embodiments of this application. The storage medium may, for example, include a memory card of a smartphone, a storage component of a tablet computer, a hard disk of a personal computer, a read-only memory (ROM), an erasable programmable read-only memory (EPROM), a portable compact disc read-only memory (CD-ROM), a USB memory, or any combination of the above storage media. The computer-readable storage medium may be any combination of one or more computer-readable storage media.

[0121] Furthermore, according to embodiments of this application, a computer program is also provided, which can be stored on a cloud or local storage medium. When this computer program is run by a computer or processor, it is used to perform the corresponding steps of the elastic imaging method of the embodiments of this application.

[0122] Although exemplary embodiments have been described herein with reference to the accompanying drawings, it should be understood that the above exemplary embodiments are merely illustrative and are not intended to limit the scope of this application. Various changes and modifications can be made therein by those skilled in the art without departing from the scope and spirit of this application. All such changes and modifications are intended to be included within the scope of this application as claimed in the appended claims.

[0123] Those skilled in the art will 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, or a combination of computer software and electronic hardware. 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.

[0124] In the several embodiments provided in this application, it should be understood that the disclosed apparatus and methods can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative. For instance, the division of units is merely a logical functional division, and in actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another apparatus, or some features may be ignored or not executed.

[0125] Numerous specific details are set forth in the specification provided herein. However, it will be understood that embodiments of this application may be practiced without these specific details. In some instances, well-known methods, structures, and techniques have not been shown in detail so as not to obscure the understanding of this specification.

[0126] Similarly, it should be understood that, in order to streamline this application and aid in understanding one or more of the various inventive aspects, features of this application may sometimes be grouped together in a single embodiment, figure, or description thereof in the description of exemplary embodiments of this application. However, this approach should not be construed as reflecting an intention that the claimed application requires more features than are expressly recited in each claim. Rather, as reflected in the corresponding claims, its inventive point lies in solving the corresponding technical problem with features fewer than all features of a single disclosed embodiment. Therefore, the claims following the detailed description are hereby expressly incorporated into that detailed description, wherein each claim itself is a separate embodiment of this application.

[0127] Those skilled in the art will understand that, apart from the mutual exclusion of features, all features disclosed in this specification (including the accompanying claims, abstract, and drawings) and all processes or units of any method or apparatus so disclosed can be combined in any combination. Unless otherwise expressly stated, each feature disclosed in this specification (including the accompanying claims, abstract, and drawings) may be replaced by an alternative feature that serves the same, equivalent, or similar purpose.

[0128] Furthermore, those skilled in the art will understand that although some embodiments described herein include certain features but not others included in other embodiments, combinations of features from different embodiments are intended to be within the scope of this application and form different embodiments. For example, in the claims, any one of the claimed embodiments can be used in any combination.

[0129] The various component embodiments of this application can be implemented in hardware, or as software modules running on one or more processors, or a combination thereof. Those skilled in the art will understand that microprocessors or digital signal processors (DSPs) can be used in practice to implement some or all of the functions of some modules according to the embodiments of this application. This application can also be implemented as an apparatus program (e.g., a computer program and computer program product) for performing part or all of the methods described herein. Such an implementation of this application can be stored on a computer-readable medium, or can be in the form of one or more signals. Such signals can be downloaded from an Internet website, provided on a carrier signal, or provided in any other form.

[0130] It should be noted that the above embodiments are illustrative of this application and not limiting of it, and that those skilled in the art can devise alternative embodiments without departing from the scope of the appended claims. In the claims, any reference signs placed between parentheses should not be construed as limiting the claims. This application can be implemented by means of hardware comprising several different elements and by means of a suitably programmed computer. In the unit claims enumerating several means, several of these means may be embodied by the same item of hardware. The use of the words first, second, and third, etc., does not indicate any order. These words can be interpreted as names.

[0131] The above description is merely a specific embodiment or illustration of the embodiments of this application. The scope of protection of this application is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this application should be included within the scope of protection of this application. The scope of protection of this application shall be determined by the scope of the claims.

Claims

1. An elastic imaging method, characterized in that, The method includes: The option provides at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponds to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponds to a second push pulse and a second ultrasound. When a selection instruction for the second elastic imaging mode is received, a second push pulse is emitted toward the target tissue of the object under test to generate a second shear wave propagating within the target tissue; A second ultrasonic wave that tracks the second shear wave is emitted toward the target tissue, and the ultrasonic echo returned by the target tissue is received to obtain ultrasonic echo data; wherein, the penetrating power of the second ultrasonic wave to the target tissue is greater than the penetrating power of the first ultrasonic wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first driving pulse to the target tissue, and the target tissue is the part of the tissue that the first shear wave or the first ultrasonic wave failed to penetrate; Based on the ultrasound echo data, a second elastic image and / or a second elastic parameter of the target tissue are obtained; Output the second elastic image and / or the second elastic parameters.

2. The elastic imaging method according to claim 1, characterized in that, The step of emitting a second push pulse to the target tissue of the object being tested includes: Adjust the delay of each element within the emission aperture of the ultrasonic probe to adjust the acoustic field shape of the second driving pulse, so that the focusing intensity of the second driving pulse is higher than that of the first driving pulse.

3. The elastic imaging method according to claim 1, characterized in that, The step of emitting a second push pulse to the target tissue of the object being tested includes: Adjust the focal point position and number of focal points of the driving pulse so that the focal intensity of the second driving pulse is higher than that of the first driving pulse.

4. The elastic imaging method according to claim 1, characterized in that, The step of emitting a second push pulse to the target tissue of the object being tested includes: The second propulsion pulse is sequentially emitted at at least two locations near the target tissue; The step of transmitting a second ultrasonic wave that tracks the second shear wave to the target tissue includes: transmitting ultrasonic waves that track each of the second shear waves to obtain at least two sets of ultrasonic echo data corresponding to at least two of the second push pulses; The step of obtaining the elastic image and / or second elastic parameter of the target tissue based on the ultrasound echo data includes: obtaining the elastic image and / or second elastic parameter based on the at least two sets of ultrasound echo data.

5. The elastic imaging method according to claim 1, characterized in that, Also includes: A first push pulse is emitted toward the target tissue of the object being tested to generate a first shear wave propagating within the target tissue; A first ultrasonic wave that tracks the first shear wave is emitted toward the target tissue, the ultrasonic echo returned by the target tissue is received, and a first elasticity image is generated. In the first elastic image, a target region that meets preset conditions is determined such that the second push pulse is emitted toward the target tissue based on the target region.

6. The elastic imaging method according to claim 5, characterized in that, The step of determining the target region that meets the preset conditions in the first elastic image includes: Identify the cavity region in the first elastic image. If the area of ​​the cavity region is greater than a preset threshold, then the cavity region is determined as the target region. The cavity region is the region that the first shear wave failed to penetrate, the region that the first ultrasonic wave failed to penetrate, or the region where the signal-to-noise ratio is lower than a preset threshold. Alternatively, the credibility of the first elastic image can be obtained, and the target region can be determined based on the credibility. Alternatively, the system may receive a user instruction to select the target region and determine the target region based on the received user instruction.

7. An elastic imaging method, characterized in that, The method includes: Acquire a first ultrasound image of the target tissue of the tested object, wherein the first ultrasound image includes a tissue structure image; In the first ultrasound image, a target region that meets the preset conditions is identified; The option provides at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponds to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponds to a second push pulse and a second ultrasound. In the second elastic imaging mode, a second push pulse is emitted toward the target tissue based on the target region to generate a second shear wave propagating within the target tissue; A second ultrasonic wave that tracks the second shear wave is emitted toward the target tissue, and the ultrasonic echo returned by the target tissue is received to obtain ultrasonic echo data; wherein, the penetrating power of the second ultrasonic wave to the target tissue is greater than the penetrating power of the first ultrasonic wave to the target tissue, and / or the penetrating power of the second shear wave to the target tissue is greater than the penetrating power of the first shear wave generated by the first driving pulse to the target tissue, and the target tissue is the part of the tissue that the first shear wave or the first ultrasonic wave failed to penetrate; Based on the ultrasound echo data, the elasticity image and / or elasticity parameters of the target tissue are obtained; Output the elasticity image and / or elasticity parameters.

8. The elastic imaging method according to claim 7, characterized in that, The target area satisfies at least one of the following preset conditions: The target region includes the type of tissue contained therein, the boundary morphology of the lesions contained therein, the area size of the lesions contained therein, the grayscale of the target region, and the brightness of the target region.

9. An ultrasound imaging system, characterized in that, The ultrasound imaging system includes: Ultrasonic probe; The transmitting circuit is used to excite the ultrasound probe to emit a driving pulse toward the target tissue of the object being measured, so as to generate a shear wave propagating within the target tissue; the transmitting circuit is also used to excite the ultrasound probe to emit ultrasound waves that track the shear wave toward the target tissue. A receiving circuit is used to control the ultrasound probe to receive the ultrasound echo returned by the target tissue in order to obtain ultrasound echo data. A human-computer interaction device for providing options for at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponding to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponding to a second push pulse and a second ultrasound. A processor for performing the elastic imaging method as described in any one of claims 1-6; A display for showing the elasticity image and / or elasticity parameters obtained by the processor.

10. An ultrasound imaging system, characterized in that, The ultrasound imaging system includes: Ultrasonic probe; The transmitting circuit is used to excite the ultrasound probe to emit a driving pulse toward the target tissue of the object being measured, so as to generate a shear wave propagating within the target tissue; the transmitting circuit is also used to excite the ultrasound probe to emit ultrasound waves that track the shear wave toward the target tissue. A receiving circuit is used to control the ultrasound probe to receive the ultrasound echo returned by the target tissue in order to obtain ultrasound echo data. A human-computer interaction device for providing options for at least two elastic imaging modes, wherein the at least two elastic imaging modes include a first elastic imaging mode and a second elastic imaging mode, the first elastic imaging mode corresponding to a first push pulse and a first ultrasound, and the second elastic imaging mode corresponding to a second push pulse and a second ultrasound. A processor for performing the elastic imaging method as described in any one of claims 7 and 8; A display for showing the elasticity image and / or elasticity parameters obtained by the processor.

Images