Ultrasonic imaging method and apparatus, computer device, medium and computer product

Abstract

The present application relates to an ultrasonic imaging method and apparatus, a computer device, a medium and a computer product. The method comprises: acquiring an ultrasonic echo signal of a target area, wherein the ultrasonic echo signal is an echo signal reflected after an ultrasonic signal of a target transmitting frequency is sent to the target area; in the target area, presetting a tracer substance, and on the basis of the size relationship of the target transmitting frequency and a preset resonance frequency range of the tracer substance, determining a target imaging mode corresponding to the target area; and within a preset duration, on the basis of the target imaging mode, carrying out signal acquisition on the ultrasonic echo signal to obtain a plurality of target tracer signals, and by means of the target imaging mode, carrying out positioning tracking on each target tracer signal to obtain a target ultrasonic image. By means of the method, a high-resolution ultrasonic image can be obtained, and the accuracy and precision of the ultrasonic image can be further improved. Moreover, the method is applied to the field of medical detection, so that the detection efficiency can be improved while the detection costs are reduced.

Description

Ultrasonic imaging method, device, computer equipment, medium and computer product

[0001] This application is based on the Chinese patent application with application number 202311714140.0 and application date December 13, 2023, and claims the priority of the aforementioned Chinese patent application. The entire content of the above-mentioned patent application is hereby introduced into this application as a reference. Technical Field

[0002] The present application relates to the field of ultrasonic imaging technology, and in particular to an ultrasonic imaging method, apparatus, computer equipment, medium, and computer product. Background Art

[0003] Ultrasonic imaging technology is an image processing technology based on the principle of ultrasound. By using ultrasonic imaging technology to detect the target object, an ultrasonic image can be obtained to display the internal structure and morphology of the target object, such as the morphology, size and position of organs or tissues.

[0004] Currently, when ultrasound imaging technology is applied to medical testing, a high-frequency ultrasound probe transmits ultrasound waves toward a target object. The high-frequency probe then collects data on the ultrasound signals reflected from the target object and analyzes the collected reflected ultrasound signals to produce a visible ultrasound image. However, existing ultrasound imaging methods often produce low-resolution images, resulting in inaccurate measurement results when the target area is small or hidden. Summary of the Invention

[0005] Based on this, it is necessary to provide an ultrasonic imaging method, device, computer equipment, medium and computer product to address the above technical problems.

[0006] In a first aspect, the present application provides an ultrasound imaging method, comprising:

[0007] Acquire an ultrasonic echo signal from the target area, where the ultrasonic echo signal is the echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area;

[0008] Preset a tracer substance in the target area, and determine a target imaging mode corresponding to the target area based on the magnitude relationship between the target emission frequency and the preset resonant frequency range of the tracer substance;

[0009] Within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain multiple target tracking signals, and each target tracking signal is processed through the target imaging mode to obtain a target ultrasonic image.

[0010] In one embodiment, the target imaging mode includes a two-dimensional fundamental wave imaging mode and a contrast imaging mode. The target imaging mode corresponding to the target area is determined based on the relationship between the target emission frequency and the preset resonant frequency range of the tracer substance, including:

[0011] When the target transmission frequency is not within the preset resonant frequency range, determining that the target imaging mode is a two-dimensional fundamental wave imaging mode, wherein the two-dimensional fundamental wave imaging mode performs ultrasonic imaging by collecting a two-dimensional fundamental wave signal in the ultrasonic echo signal;

[0012] When the target transmission frequency is within the preset resonant frequency range, the target imaging mode is determined to be a contrast imaging mode, wherein the contrast imaging mode performs ultrasound imaging by collecting contrast signals in ultrasound echo signals.

[0013] In one embodiment, the two-dimensional fundamental wave signal includes a tissue signal and a first tracer signal, and the ultrasonic echo signal is collected according to a target imaging mode to obtain a target tracer signal, including:

[0014] In the two-dimensional fundamental wave imaging mode, the ultrasonic echo signal is collected according to the two-dimensional fundamental wave imaging mode to obtain a two-dimensional fundamental wave signal;

[0015] The two-dimensional fundamental wave signal is subjected to time-space filtering and frequency filtering respectively to filter out the tissue signal and obtain a first tracing signal.

[0016] In one embodiment, within a preset time period, ultrasound echo signals are collected according to a target imaging mode to obtain multiple target tracking signals, including:

[0017] Within a preset time period, a number of initial tracer signals are obtained based on the movement of the tracer substance in the target area;

[0018] Acquiring state parameters of each initial tracer signal, wherein the state parameters include position parameters, direction parameters, and speed parameters;

[0019] When the state parameters meet the preset parameter conditions, multiple target tracking signals are obtained.

[0020] In one embodiment, before acquiring the ultrasonic echo signal of the target area, the method includes:

[0021] Acquire a first ultrasonic echo signal of the target object, where the first ultrasonic echo signal is an echo signal reflected after an ultrasonic signal is sent to the target object;

[0022] A first ultrasonic image is obtained according to the first ultrasonic echo signal. When a region of interest exists in the first ultrasonic image, the region of interest is used as a target region.

[0023] In one embodiment, processing the target tracking signal by a target imaging mode to obtain a target ultrasound image includes:

[0024] Acquiring a first preprocessing parameter for controlling the number and intensity of bright spots in an ultrasound image, and a second preprocessing parameter for compensating for motion of a target object;

[0025] Positioning and tracking each target tracer signal according to the first preprocessing parameter and the second preprocessing parameter to obtain an initial ultrasound image;

[0026] Acquiring image processing parameters, wherein the image processing parameters include image resolution, image contrast, image filtering, and image enhancement;

[0027] The initial ultrasound image is processed according to the image processing parameters to obtain a target ultrasound image.

[0028] In a second aspect, the present application further provides an ultrasonic imaging device, comprising:

[0029] The receiving module is used to obtain the ultrasonic echo signal of the target area. The ultrasonic echo signal is the echo signal reflected after the ultrasonic signal of the target transmission frequency is sent to the target area, and the target transmission frequency of the ultrasonic signal is determined;

[0030] An imaging mode determination module is used to preset a tracer substance in a target area and determine a target imaging mode corresponding to the target area based on the relationship between the target emission frequency and the preset resonant frequency range of the tracer substance;

[0031] The imaging module is used to collect ultrasonic echo signals according to the target imaging mode within a preset time period to obtain multiple target tracking signals, and locate and track each target tracking signal through the target imaging mode to obtain a target ultrasonic image.

[0032] In a third aspect, the present application further provides a computer device comprising a memory and a processor, wherein the memory stores a computer program, and when the processor executes the computer program, the following steps are implemented:

[0033] Acquire an ultrasonic echo signal from the target area, where the ultrasonic echo signal is the echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area;

[0034] Preset a tracer substance in the target area, and determine a target imaging mode corresponding to the target area based on the magnitude relationship between the target emission frequency and the preset resonant frequency range of the tracer substance;

[0035] Within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain multiple target tracking signals, and each target tracking signal is located and tracked through the target imaging mode to obtain a target ultrasonic image.

[0036] In a fourth aspect, the present application further provides a computer-readable storage medium having a computer program stored thereon, wherein when the computer program is executed by a processor, the following steps are implemented:

[0037] Acquire an ultrasonic echo signal from the target area, where the ultrasonic echo signal is the echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area;

[0038] Preset a tracer substance in the target area, and determine a target imaging mode corresponding to the target area based on the magnitude relationship between the target emission frequency and the preset resonant frequency range of the tracer substance;

[0039] Within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain multiple target tracking signals, and each target tracking signal is located and tracked through the target imaging mode to obtain a target ultrasonic image.

[0040] In a fifth aspect, the present application further provides a computer program product, comprising a computer program, which, when executed by a processor, implements the following steps:

[0041] Acquire an ultrasonic echo signal from the target area, where the ultrasonic echo signal is the echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area;

[0042] Preset a tracer substance in the target area, and determine a target imaging mode corresponding to the target area based on the magnitude relationship between the target emission frequency and the preset resonant frequency range of the tracer substance;

[0043] Within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain multiple target tracking signals, and each target tracking signal is located and tracked through the target imaging mode to obtain a target ultrasonic image.

[0044] The above-mentioned ultrasonic imaging method, apparatus, computer equipment, medium and computer product obtain an ultrasonic echo signal from a target area. The ultrasonic echo signal is the echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area; a tracer substance is preset in the target area, and a target imaging mode corresponding to the target area is determined based on the size relationship between the target transmission frequency and the preset resonant frequency range of the tracer substance; within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain multiple target tracer signals, and each target tracer signal is located and tracked through the target imaging mode to obtain a target ultrasonic image. The method determines the working mode during the ultrasonic imaging process based on the target transmission frequency corresponding to the ultrasonic signal, and can achieve high-resolution ultrasonic images at any target transmission frequency. Based on the tracer substance, the accuracy and precision of the ultrasonic image can be improved for small target areas or hidden key areas, such as ultrasonic imaging of microvascular networks. At the same time, the method can be applied to the field of medical testing, which can reduce testing costs and improve testing efficiency. BRIEF DESCRIPTION OF THE DRAWINGS

[0045] In order to more clearly illustrate the technical solutions in the embodiments of the present application or related technologies, the following briefly introduces the drawings required for use in the embodiments or related technical descriptions. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0046] FIG1 is a diagram illustrating an application environment of an ultrasonic imaging method according to an embodiment;

[0047] FIG2 is a schematic flow chart of an ultrasound imaging method according to an embodiment;

[0048] FIG3 is a schematic diagram of the density corresponding to the tracer substance in one embodiment;

[0049] FIG4 is a schematic diagram of a data analysis page in one embodiment;

[0050] FIG5 is a schematic flow chart of an ultrasound imaging method according to another embodiment;

[0051] FIG6 is a block diagram of an ultrasonic imaging device according to an embodiment;

[0052] FIG7 is a schematic diagram of an ultrasound image display page in one embodiment;

[0053] FIG8 is a flowchart of a two-dimensional fundamental wave ultrasound imaging mode according to one embodiment;

[0054] FIG9 is a schematic diagram of an ultrasound image mode control page in one embodiment;

[0055] FIG10 is a schematic diagram of a data collection page in one embodiment;

[0056] FIG11 is a schematic diagram of a data collection progress page in one embodiment;

[0057] FIG12 is a schematic diagram of a data acquisition control page in one embodiment;

[0058] FIG13 is a schematic diagram of a page for determining an area of ​​interest in one embodiment;

[0059] FIG14 is a flowchart of a workflow of a contrast ultrasound imaging mode according to one embodiment;

[0060] FIG15 is a schematic diagram of a data collection page in another embodiment;

[0061] FIG16 is a block diagram of the structure of an ultrasonic imaging device according to one embodiment;

[0062] FIG17 is a diagram showing the internal structure of a computer device as a terminal in one embodiment;

[0063] FIG18 is a diagram showing the internal structure of a computer device that is a server in one embodiment. DETAILED DESCRIPTION

[0064] In order to make the purpose, technical solutions and advantages of this application more clear, the following further describes this application in detail with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain this application and are not intended to limit this application.

[0065] The ultrasound imaging method provided in an embodiment of the present application can be applied in the application environment shown in FIG1 . Terminal 102 communicates with server 104 via a network. A data storage system can store data that server 104 needs to process. The data storage system can be integrated with server 104 or placed on a cloud or other network server. An ultrasonic echo signal is acquired from a target area. The ultrasonic echo signal is the echo signal reflected after an ultrasonic signal at a target transmission frequency is transmitted to the target area. A tracer substance is pre-set in the target area, and a target imaging mode corresponding to the target area is determined based on the relationship between the target transmission frequency and the preset resonant frequency range of the tracer substance. Within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain multiple target tracer signals. Each target tracer signal is located and tracked using the target imaging mode to obtain a target ultrasound image. Terminal 102 can be, but is not limited to, various personal computers, laptops, smartphones, tablets, Internet of Things devices, and portable wearable devices. Internet of Things devices can include smart speakers, smart TVs, smart air conditioners, smart car devices, etc. Portable wearable devices can include smart watches, smart bracelets, head-mounted devices, etc. The server 104 may be implemented as an independent server or a server cluster consisting of multiple servers.

[0066] In an exemplary embodiment, as shown in FIG2 , an ultrasound imaging method is provided, which is described by taking the method applied to the terminal 102 in FIG1 as an example, and includes the following steps 202 to 206 . In particular:

[0067] Step 202 : Acquire an ultrasonic echo signal of the target area. The ultrasonic echo signal is an echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area.

[0068] For example, the method is applied to an ultrasonic imaging device. In the ultrasonic imaging device, the ultrasonic imaging device includes a probe, a host, an operating panel, a touch screen, and a display screen. Taking the area of ​​the target object with pathological features as the target area as an example, the probe in the ultrasonic imaging device transmits an ultrasonic signal of a target transmission frequency to the target area and receives an ultrasonic echo signal. Specifically, the ultrasonic signal is reflected in different tissue structures in the target area, or at the interface between tissue structures of different types and densities, and the reflected echo signal is received by the probe in the ultrasonic imaging device.

[0069] Step 204 : preset a tracer substance in the target area, and determine a target imaging mode corresponding to the target area according to a magnitude relationship between the target emission frequency and the preset resonant frequency range of the tracer substance.

[0070] Tracer materials are used to enhance ultrasound images and can be tiny gas sacs, tiny bubbles, or other visible substances. Resonant frequency refers to the frequency at which a substance oscillates most strongly in the ultrasonic field generated by an ultrasound signal.

[0071] Exemplarily, a preset resonant frequency range is determined based on the resonant frequencies of different tracer substances, and tracer substances are preset in the microvessels of the target area. The tracer substances can move in the microvessels, and the ultrasonic signal is also reflected at the position of the tracer substances. The echo signal reflected by the tracer substances is used as the ultrasonic echo signal corresponding to the tracer substances.

[0072] When the target transmission frequency of the ultrasonic signal is within the preset resonant frequency range, there is a strong resonant reaction between the ultrasonic signal and the tracer material, and the intensity or energy of the ultrasonic echo signal corresponding to the tracer material is high. When the tracer material moves in the target area, the contrast imaging mode is used for signal acquisition, which can effectively acquire the ultrasonic echo signal corresponding to the tracer material, and the signal-to-noise ratio of the ultrasonic image is high; when the target transmission frequency of the ultrasonic signal is outside the preset resonant frequency range, the resonant reaction between the ultrasonic signal and the tracer material is weak. When the tracer material moves in the target area, if the contrast imaging mode is used, only a weak tracer material echo signal can be acquired, and the signal-to-noise ratio of the ultrasonic image is low. Therefore, when the target transmission frequency of the ultrasonic signal is outside the preset resonant frequency range, the two-dimensional fundamental wave imaging mode is used for signal acquisition.

[0073] Step 206 : within a preset time period, collect the ultrasonic echo signal according to the target imaging mode to obtain a plurality of target tracking signals, locate and track each target tracking signal through the target imaging mode to obtain a target ultrasonic image.

[0074] The target tracer signal is an ultrasonic echo signal corresponding to the tracer material, and the target ultrasonic image can be a density map, a direction map, and a velocity map of the tracer material.

[0075] Illustratively, in contrast imaging mode, the ultrasonic echo signal corresponding to the tracer substance can be directly collected to obtain a target tracer signal, and the position of the tracer substance in the target area can be determined based on the target tracer signal; in two-dimensional fundamental wave imaging mode, the ultrasonic echo signal is collected to obtain a two-dimensional fundamental wave signal, wherein the two-dimensional fundamental wave signal includes the ultrasonic echo signal corresponding to the tracer substance and the ultrasonic echo signal corresponding to the tissue structure. The two-dimensional fundamental wave signal is processed to obtain an ultrasonic echo signal corresponding to the tracer substance, that is, the target tracer signal.

[0076] During the preset data acquisition time, the tracer material moves in the target area, and the target tracer signal corresponding to each movement moment can be collected. By positioning and tracking the target tracer signal, the spatial position of the tracer material can be determined. The speed and direction of the tracer material can be quantitatively calculated based on the movement of the target tracer signal, and the movement trajectory of the target tracer signal corresponding to each movement moment can be accumulated to obtain the density map, speed map and direction map of the tracer material in the target area. By determining the position change of the tracer material in the target area, the movement video of the tracer material can be obtained. Figure 3 is a schematic diagram of the density map.

[0077] In the above-mentioned ultrasound imaging method, at a specific ultrasound signal transmission frequency, an ultrasound echo signal of the target area can be obtained. The ultrasound echo signal is the echo signal reflected after the ultrasound signal is sent to the target area at the target transmission frequency; a tracer substance is preset in the target area, and the target imaging mode corresponding to the target area is determined based on the relationship between the target transmission frequency and the preset resonant frequency range of the tracer substance; within a preset time period, the ultrasound echo signal is collected according to the target imaging mode to obtain multiple target tracer signals, and each target tracer signal is processed according to the target imaging mode to obtain a target ultrasound image. This method determines the operating mode during the ultrasound imaging process based on the transmission frequency corresponding to the ultrasound signal, and can achieve high-resolution ultrasound images at any transmission frequency. Based on the tracer substance, the accuracy and precision of ultrasound images can be improved for small target areas or hidden key areas, such as ultrasound imaging of microvascular networks. At the same time, this method can be applied to the field of medical testing, reducing testing costs while improving testing efficiency.

[0078] In one embodiment, the target imaging mode includes a two-dimensional fundamental wave imaging mode and a contrast imaging mode. The target imaging mode corresponding to the target area is determined according to the size relationship between the target emission frequency and the preset resonant frequency range of the tracer substance, including: when the target emission frequency is not within the preset resonant frequency range, the target imaging mode is determined to be a two-dimensional fundamental wave imaging mode, wherein the two-dimensional fundamental wave imaging mode performs ultrasonic imaging by collecting the two-dimensional fundamental wave signal in the ultrasonic echo signal; when the target emission frequency is within the preset resonant frequency range, the target imaging mode is determined to be a contrast imaging mode, wherein the contrast imaging mode performs ultrasonic imaging by collecting the contrast signal in the ultrasonic echo signal.

[0079] A two-dimensional fundamental signal refers to a fundamental signal propagating in two spatial dimensions, such as the x-axis and y-axis. The fundamental signal is the lowest-frequency component in the signal's spectrum. A contrast signal refers to an ultrasonic echo signal associated with a tracer substance, such as a contrast tracer, that is collected and used for imaging during ultrasound imaging.

[0080] For example, when the target transmission frequency is outside the preset resonant frequency range, a two-dimensional fundamental wave imaging mode is used to collect the two-dimensional fundamental wave signal in the ultrasonic echo signal. In this imaging mode, the two-dimensional fundamental wave signal includes echo signals derived from reflection, scattering, and diffraction of the ultrasonic signal by different tissue structures in the target area. Therefore, the ultrasonic image includes tissue information of each tissue structure in the target area. For example, when the tracer material is a microbubble containing an inert gas, there is a large difference in acoustic impedance between the tracer material and the tissue structure. The echo signal reflected by the tissue structure from the ultrasonic signal has a high intensity, which can remove noise signals from the echo signal. Acoustic impedance refers to the propagation barrier that exists when ultrasonic waves propagate between different tissue structures. The echo signals generated by the acoustic impedance of different tissue structures can distinguish and determine tissue structure and tissue function. Furthermore, when the tracer substance moves in the target area, for example, when the tracer substance moves with blood in the tissue vascular network, there is an obvious difference in the movement of the tracer substance and the movement of other extravascular tissue structures. Therefore, the ultrasonic echo signal obtained during the movement of the tracer substance can be distinguished from the ultrasonic echo signal obtained during the movement of the tissue structure, and then the first tracer signal corresponding to the tracer substance can be determined in the two-dimensional fundamental wave signal.

[0081] When the target transmission frequency is within the preset resonant frequency range, a contrast imaging mode is used. In this mode, the ultrasonic signal undergoes pulse inversion, amplitude modulation, and contrast pulse sequence processing to generate a target ultrasonic signal sequence, which exhibits different apertures and polarities. After transmitting the target ultrasonic signal sequence to the target area, it is superimposed with the ultrasonic echo signal, suppressing the ultrasonic echo signals corresponding to tissue structures with smaller movement amplitudes. This allows the ultrasonic echo signals corresponding to the movement of the tracer material used for ultrasonic imaging to be directly obtained, i.e., the contrast signal.

[0082] In this embodiment, different ultrasonic echo signals are collected in different ultrasonic imaging modes. Based on the characteristics of these different ultrasonic echo signals, the ultrasonic echo signals associated with the tracer substance, i.e., the tracer signal, can be effectively separated. Due to the excellent separation of the tracer signal, the position of the tracer substance can be tracked based on the tracer signal, thereby obtaining a high-resolution ultrasonic image of the target area. Furthermore, if this method is applied to the field of medical testing, in contrast imaging mode, contrast signals and tracer signals can be simultaneously collected. Conventional contrast imaging mode detection and analysis can be achieved based on the contrast signal, while super-resolution contrast imaging mode detection and analysis can be achieved based on the tracer signal, thereby reducing testing costs while improving testing efficiency.

[0083] In one embodiment, the two-dimensional fundamental wave signal includes a tissue signal and a first tracer signal, and the ultrasonic echo signal is acquired according to a target imaging mode to obtain a target tracer signal, including: in a two-dimensional fundamental wave imaging mode, the ultrasonic echo signal is acquired according to the two-dimensional fundamental wave imaging mode to obtain a two-dimensional fundamental wave signal; and the two-dimensional fundamental wave signal is subjected to spatiotemporal filtering processing and frequency filtering processing respectively to filter out the tissue signal to obtain the first tracer signal.

[0084] Among them, spatiotemporal filtering refers to filtering the grayscale value of each pixel in the ultrasound image, combining or calculating the pixel values ​​around each pixel in the original ultrasound image to obtain the target ultrasound image corresponding to the new pixel value. Spatiotemporal filtering can be used for image enhancement and image noise reduction. Frequency filtering refers to Fourier transforming the ultrasound image, converting the ultrasound image from the time domain to the frequency domain, then filtering in the frequency domain, and finally converting the ultrasound image back to the time domain through inverse Fourier transform to obtain the filtered ultrasound image. Frequency filtering can be used for image denoising, frequency domain enhancement, and image restoration.

[0085] For example, as described in the aforementioned embodiments, in a two-dimensional fundamental wave imaging mode, an ultrasonic echo signal of a tissue structure, i.e., a tissue signal, can be acquired, and an ultrasonic echo signal corresponding to a tracer substance, i.e., a first tracer signal, can also be acquired. Filtering is performed on the two-dimensional fundamental wave signal to remove the tissue signal from the two-dimensional fundamental wave signal, thereby obtaining the first tracer signal. Specifically, in the spatiotemporal filtering process, a spatiotemporal filtering method based on time difference is employed. This spatiotemporal filtering method is based on the fact that the time delay of the tracer signal propagating in the target region is different from the time delay of the tissue signal in the tissue structure. By acquiring multiple frames of the two-dimensional fundamental wave signal and performing time difference on the two-dimensional fundamental wave signal, a set of time difference images is obtained. The time difference images are then processed through frequency domain filtering to separate the tissue signal from the tracer signal. For example, a high-pass filter can be used to suppress the low-frequency components of the tissue signal while retaining the high-frequency tracer signal, thereby obtaining the first tracer signal in the two-dimensional fundamental wave imaging mode.

[0086] In this embodiment, spatiotemporal filtering and frequency filtering can be tailored to the characteristics of tissue signals. By filtering out interference from tissue signals, the first tracer signal becomes more prominent, helping to improve the contrast and clarity of ultrasound images. Filtering can also enhance the intensity and visibility of the first tracer signal, facilitating accurate detection and localization of tracer substances. Filtering can also help improve the spatial and frequency resolution of ultrasound images, reducing image blur and artifacts by removing noise, and providing more accurate and detailed image information.

[0087] In one embodiment, within a preset time period, ultrasonic echo signals are collected according to a target imaging mode to obtain multiple target tracer signals, including: within the preset time period, according to the movement of the tracer material in the target area, a number of initial tracer signals are obtained; state parameters of each initial tracer signal are obtained, wherein the state parameters include position parameters, direction parameters and speed parameters; when the state parameters meet preset parameter conditions, multiple target tracer signals are obtained.

[0088] The initial tracer signal is the ultrasonic echo signal of the tracer material.

[0089] Exemplarily, a data acquisition time corresponding to a target imaging mode is determined and used as a preset duration. For example, assuming the target imaging mode is a 2D fundamental wave imaging mode, the ultrasound imaging device can perform multiple data acquisition operations on the 2D fundamental wave signal of the target area based on the 2D fundamental wave imaging mode. Each data acquisition operation can acquire one or more 2D fundamental wave signals. Filtering each 2D fundamental wave signal can generate multiple initial tracer signals. The initial tracer signals include a data acquisition tag that indicates the data acquisition time or number of data acquisition rounds corresponding to the initial tracer signal. The position, direction, and speed of the tracer substance in the target area can be determined based on the initial tracer signal. Based on the data acquisition tag, the position, direction, and speed of each initial tracer signal are compared. For example, if the speed of the tracer substance at the second moment is much greater than the speed of the tracer substance at other moments, or the speed of the tracer substance at the second moment is greater than a preset speed value; or the position of the tracer substance at the second moment is much farther away from the position of the tracer substance at other moments than a preset distance value; or the direction of the tracer substance at the second moment is different from the direction of the tracer substance at other moments, the initial tracer signal corresponding to the tracer substance at the second moment can be considered an abnormal signal. The initial tracer signal at the second moment is deleted from the initial tracer signal to obtain multiple target tracer signals.

[0090] In this embodiment, based on preset parameter conditions, abnormal initial tracer signals can be eliminated, reducing noise and artifacts in the image, thereby improving image quality and clarity. During the tracking process of the initial tracer signal, eliminating abnormal initial tracer signals can improve the tracking effect of the tracer substance and enhance the stability and reliability of the ultrasound image.

[0091] In one embodiment, before obtaining the ultrasonic echo signal of the target area, the method includes: obtaining a first ultrasonic echo signal of the target object, where the first ultrasonic echo signal is an echo signal reflected after an ultrasonic signal is sent to the target object; obtaining a first ultrasonic image based on the first ultrasonic echo signal, and if a region of interest exists in the first ultrasonic image, using the region of interest as the target area.

[0092] For example, an ultrasonic imaging device transmits an ultrasonic signal to a target object and receives a first ultrasonic echo signal, which is generated after the target object reflects the ultrasonic signal. Based on the first ultrasonic echo signal, the target object can be comprehensively detected to obtain a first ultrasonic image corresponding to the target object. Based on the first ultrasonic image, an area with pathological features can be identified as a region of interest (ROI). A high-resolution ultrasonic imaging mode is then used on the region of interest to obtain a target ultrasound image.

[0093] In this embodiment, after determining the target area of ​​the target object based on the region of interest, the ultrasonic imaging process of the target area is performed, which can reduce the amount of data analysis of the ultrasonic imaging, reduce the analysis time and analysis cost, and improve the work efficiency of the ultrasonic imaging process.

[0094] In one embodiment, target tracer signals are processed through a target imaging mode to obtain a target ultrasound image, including: obtaining a first preprocessing parameter for controlling the number and intensity of bright spots in the ultrasound image, and a second preprocessing parameter for compensating for the motion of the target object; analyzing each target tracer signal according to the first preprocessing parameter and the second preprocessing parameter to obtain an initial ultrasound image; obtaining image processing parameters, wherein the image processing parameters include image resolution, image contrast, image filtering, and image enhancement; and performing image processing on the initial ultrasound image according to the image processing parameters to obtain a target ultrasound image.

[0095] For example, as shown in FIG4 , during ultrasound imaging of a target area, while analyzing the target tracer signal to obtain an ultrasound image, a first preprocessing parameter, such as the Vspeckle parameter corresponding to a special adaptive imaging processing technique, can be obtained. A smaller Vspeckle parameter indicates a greater amount of information in the ultrasound image obtained through signal analysis and a higher level of noise. A larger Vspeckle parameter indicates a lower amount of information in the ultrasound image obtained through signal analysis and a lower level of noise, resulting in a cleaner ultrasound image. A second preprocessing parameter, such as a motion compensation parameter associated with a motion compensation algorithm, is obtained. The second preprocessing parameter is determined based on the movement of tissue structures during data acquisition. A smaller motion compensation parameter weakens the motion compensation algorithm's ability to suppress tissue movement during data acquisition, but also reduces the computational complexity of the target tracer signal and shortens the analysis time. A larger motion compensation parameter increases the motion compensation algorithm's ability to suppress tissue movement during data acquisition and increases the analysis time. Based on ultrasound imaging requirements, first and second preprocessing parameters are determined. Signal analysis of each target tracer signal is performed using the first and second preprocessing parameters to obtain an initial ultrasound image corresponding to the target area. Image processing is performed on the initial ultrasound image. The image processing may include adjusting image processing parameters such as image resolution, contrast, spatial smoothing, and vascular enhancement to obtain a target ultrasound image.

[0096] Furthermore, measurements can be performed on the target ultrasound image. For example, if a tracer substance is moving within the microvessels of the target area, parameters such as microvascular diameter, spacing, density, complexity, tortuosity, and perfusion index can be measured. Furthermore, to improve the accuracy of the measurement results and the accuracy of the microvascular network, the initial ultrasound image can be amplified. This amplification process dynamically increases the resolution and displayed detail of the initial ultrasound image, improving the accuracy of the measurement results.

[0097] In this embodiment, during ultrasound imaging, movement of the target object's tissue structure can cause blurring or artifacts in the ultrasound image. Motion compensation technology can correct for motion-induced image distortion, improving image clarity and accuracy. After acquiring the ultrasound image, adjustments to parameters such as brightness, color, and filtering can improve image quality and readability, enhancing the signal-to-noise ratio and clarity.

[0098] In an exemplary embodiment, as shown in FIG5 , an ultrasound imaging method is provided. The method is applied to the ultrasound imaging device shown in FIG6 , and the method includes:

[0099] Step 502: Acquire a first ultrasonic echo signal of the target object. The first ultrasonic echo signal is an echo signal reflected after an ultrasonic signal is sent to the target object. A first ultrasonic image is obtained based on the first ultrasonic echo signal. If a region of interest exists in the first ultrasonic image, the region of interest is used as the target region.

[0100] Step 504 : Acquire an ultrasonic echo signal of the target area. The ultrasonic echo signal is an echo signal reflected after an ultrasonic signal is sent to the target area. Determine a target transmission frequency of the ultrasonic signal.

[0101] In step 506, a tracer material is placed in the target area. When the target emission frequency is not within the preset resonant frequency range, the target imaging mode corresponding to the target area is determined to be a two-dimensional fundamental wave imaging mode. The two-dimensional fundamental wave imaging mode performs ultrasonic imaging by acquiring two-dimensional fundamental wave signals from ultrasonic echo signals. Within a preset time period, the tracer material is controlled to move within the target area. In the two-dimensional fundamental wave imaging mode, the ultrasonic echo signals are acquired according to the two-dimensional fundamental wave imaging mode to obtain multiple two-dimensional fundamental wave signals. Each two-dimensional fundamental wave signal is subjected to spatiotemporal filtering and frequency filtering to filter out tissue signals, thereby obtaining multiple initial tracer signals.

[0102] Alternatively, a tracer material is pre-set in the target area. When the target emission frequency is within a preset resonant frequency range, the target imaging mode corresponding to the target area is determined to be a contrast imaging mode. The contrast imaging mode performs ultrasonic imaging by acquiring contrast signals from ultrasonic echo signals. Within a preset time period, the tracer material is controlled to move within the target area. In the contrast imaging mode, the ultrasonic echo signals are acquired according to the contrast imaging mode to obtain multiple contrast signals, i.e., multiple initial tracer signals.

[0103] 6 , the ultrasonic imaging device 600 includes a probe 602, a display screen 604, a touch screen 606, an operating panel 608, a base 610, and a host 612, wherein the host 612 is respectively connected to the probe 602, the display screen 604, the touch screen 606, the operating panel 608, and the base 610. The display screen 604 is used to display diagnostic information. As shown in FIG7 , the display screen 604 includes an image display area, a target object information management area, and an image parameter area. The image display area is used to display ultrasonic images, the image parameter area is used to display parameters corresponding to the ultrasonic images, and the target object information management area is used to display information about the target objects. The touch screen 606 and the operating panel 608 are used to select and implement different applications or functions. The host 612 includes hardware such as a processor, a motherboard, and a hard disk, which are used to control the ultrasonic imaging device 600. The chassis 610 is used to fix or move the ultrasonic imaging device 600, and the ultrasonic imaging device 600 can be freely moved by the rollers of the chassis.

[0104] Taking the tracer substance as a contrast tracer as an example, the contrast tracer moves in the microvascular network of the target area, and the probe 602 of the ultrasonic imaging device 600 can adopt multiple ultrasonic imaging modes, including two-dimensional fundamental wave imaging, color Doppler imaging, and power Doppler imaging. If the probe 602 is a high-frequency probe, the amplitude of the contrast tracer resonance phenomenon is relatively weak at a higher ultrasonic transmission frequency. At this time, the ultrasonic imaging device 600 operates in the two-dimensional fundamental wave ultrasonic imaging mode. FIG8 is a flowchart of the workflow corresponding to the two-dimensional fundamental wave ultrasonic imaging mode. In the display screen page shown in FIG9, click the ultrasonic imaging button to respond to the instruction to start the two-dimensional fundamental wave ultrasonic imaging mode, start the ultrafast plane wave fundamental wave imaging, and complete the data acquisition preparation. After clicking the ultrasonic imaging button, enter the display screen page shown in FIG10. After determining the preset acquisition time on this display screen page, click the data acquisition button to respond to the data acquisition instruction and perform data acquisition on the two-dimensional fundamental wave signal. During the data acquisition process, as shown in Figure 11, the display screen page can display the data acquisition progress in real time. When the progress bar reaches 100%, the data acquisition process is completed, and a set of two-dimensional fundamental wave signal data is obtained. At the same time, a marker image corresponding to the two-dimensional fundamental wave signal data can be generated in the target object information management area of ​​display screen 604. If the preset acquisition time is long, you can click the Cancel button below the progress bar to cancel the data acquisition instruction and manually end the data acquisition process. Multiple sets of two-dimensional fundamental wave signal data can be obtained. Click the generated marker image to play back the marker image on the display screen page. On the display screen page shown in Figure 12, click the Data Analysis button to respond to the Data Analysis instruction. Based on the motion differences between the contrast tracer and tissue structure, the contrast tracer signal and tissue signal can be separated through signal processing methods such as subtraction and filtering to obtain contrast tracer signal data. According to the first frame of two-dimensional image corresponding to the first set of two-dimensional fundamental wave signal data, in the data analysis interface shown in Figure 13, the region of interest can be selected on the first frame of two-dimensional image. When the region of interest is not selected, the frame boundary is displayed as a dotted line. In the dotted line state, the size and position of the region of interest can be edited. After the region of interest is determined, the frame boundary is displayed as a solid line, and the ultrasound image corresponding to the region of interest is obtained.

[0105] If probe 602 is a medium-low frequency probe, the contrast tracer resonance phenomenon is significant at relatively low medium-low frequency ultrasonic transmission frequencies. In this case, the ultrasonic imaging device 600 operates in contrast ultrasound imaging mode. FIG14 shows a workflow diagram corresponding to the contrast ultrasound imaging mode. In contrast ultrasound imaging mode, a special transmission sequence can effectively suppress tissue signals with smaller motion amplitudes, and the collected contrast signal is simply filtered, resulting in good separation of the contrast tracer signal and high-resolution ultrasound images. In contrast imaging mode, as shown in FIG15 , by clicking the data acquisition button and responding to the data acquisition instruction, you can also simultaneously click the start button corresponding to the contrast data and respond to the start instruction to simultaneously acquire contrast data corresponding to the contrast signal and tracer signal data corresponding to the contrast tracer signal.

[0106] Step 508 : obtaining state parameters of each initial tracking signal, wherein the state parameters include position parameters, direction parameters, and speed parameters; and obtaining multiple target tracking signals when the state parameters meet preset parameter conditions.

[0107] Step 510: Obtain a first preprocessing parameter for controlling the number and intensity of bright spots in the ultrasound image, and a second preprocessing parameter for compensating for the motion of the target object; analyze each target tracking signal according to the first preprocessing parameter and the second preprocessing parameter to obtain an initial ultrasound image.

[0108] Step 512: Acquire image processing parameters, wherein the image processing parameters include image resolution, image contrast, image filtering, and image enhancement; perform image processing on the initial ultrasound image according to the image processing parameters to obtain a target ultrasound image.

[0109] In this embodiment, an ultrasonic echo signal from a target area is acquired. The ultrasonic echo signal is the echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area. A tracer substance is preset in the target area, and a target imaging mode corresponding to the target area is determined based on the relationship between the target transmission frequency and the preset resonant frequency range of the tracer substance. Within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain multiple target tracer signals. Each target tracer signal is located and tracked using the target imaging mode to obtain a target ultrasonic image. This method determines the operating mode during the ultrasonic imaging process based on the target transmission frequency corresponding to the ultrasonic signal, and can achieve high-resolution ultrasonic images at any target transmission frequency. Based on the tracer substance, the accuracy and precision of ultrasonic images can also be improved for very small target areas or hidden key areas, such as ultrasonic imaging of microvascular networks. Moreover, if this method is applied to the field of medical detection, in the contrast imaging mode, the contrast signal and the tracer signal can be collected simultaneously. The detection and analysis of the conventional contrast mode can be realized based on the contrast signal, and the detection and analysis of the super-resolution contrast imaging mode can be realized based on the tracer signal, which can reduce the detection cost while improving the detection efficiency.

[0110] It should be understood that, although the various steps in the flowcharts involved in the various embodiments described above are displayed in sequence according to the instructions of the arrows, these steps are not necessarily executed in sequence in the order indicated by the arrows. Unless otherwise specified herein, there is no strict order restriction on the execution of these steps, and these steps can be executed in other orders. Moreover, at least a portion of the steps in the flowcharts involved in the various embodiments described above can include multiple steps or multiple stages, and these steps or stages are not necessarily executed and completed at the same time, but can be executed at different times, and the execution order of these steps or stages is not necessarily to be carried out in sequence, but can be executed in turn or alternately with other steps or at least a portion of steps or stages in other steps.

[0111] Based on the same inventive concept, embodiments of the present application further provide an ultrasonic imaging device for implementing the ultrasonic imaging method described above. The solution provided by this device is similar to the solution described in the method described above. Therefore, the specific limitations of one or more ultrasonic imaging device embodiments provided below can be found in the above-described limitations of the ultrasonic imaging method and will not be further elaborated here.

[0112] In an exemplary embodiment, as shown in FIG16 , an ultrasound imaging device 1600 is provided, comprising: a receiving module 1602 , an imaging mode determination module 1604 , and an imaging module 1606 , wherein:

[0113] The receiving module 1602 is used to obtain an ultrasonic echo signal of the target area. The ultrasonic echo signal is an echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area.

[0114] An imaging mode determination module 1604 is configured to preset a tracer substance in a target area and determine a target imaging mode corresponding to the target area based on a relationship between a target emission frequency and a preset resonant frequency range of the tracer substance;

[0115] The imaging module 1606 is used to collect ultrasonic echo signals according to the target imaging mode within a preset time period to obtain multiple target tracking signals, and locate and track each target tracking signal through the target imaging mode to obtain a target ultrasonic image.

[0116] In one embodiment, the target imaging mode includes a two-dimensional fundamental wave imaging mode and a contrast imaging mode. The imaging mode determination module 1604 is further used to determine that the target imaging mode is a two-dimensional fundamental wave imaging mode when the target transmission frequency is not within a preset resonant frequency range, wherein the two-dimensional fundamental wave imaging mode performs ultrasonic imaging by collecting a two-dimensional fundamental wave signal in an ultrasonic echo signal; when the target transmission frequency is within a preset resonant frequency range, the target imaging mode is determined to be a contrast imaging mode, wherein the contrast imaging mode performs ultrasonic imaging by collecting a contrast signal in an ultrasonic echo signal.

[0117] In one embodiment, the two-dimensional fundamental wave signal includes a tissue signal and a first tracer signal. The imaging module 1606 is further used to acquire the ultrasonic echo signal according to the two-dimensional fundamental wave imaging mode in the two-dimensional fundamental wave imaging mode to obtain the two-dimensional fundamental wave signal; and perform time-space filtering and frequency filtering on the two-dimensional fundamental wave signal to filter out the tissue signal to obtain the first tracer signal.

[0118] In one embodiment, the imaging module 1606 is further configured to obtain a plurality of initial tracer signals based on the movement of the tracer material in the target area within a preset time period; obtain state parameters of each initial tracer signal, wherein the state parameters include position parameters, direction parameters, and speed parameters; and obtain a plurality of target tracer signals when the state parameters meet preset parameter conditions.

[0119] In one embodiment, the device is also used to obtain a first ultrasonic echo signal of the target object, which is an echo signal reflected after an ultrasonic signal is sent to the target object; a first ultrasonic image is obtained based on the first ultrasonic echo signal, and if there is a region of interest in the first ultrasonic image, the region of interest is used as the target area.

[0120] In one embodiment, the imaging module 1606 is further used to obtain a first preprocessing parameter for controlling the number and intensity of bright spots in the ultrasound image, and a second preprocessing parameter for compensating for the movement of the target object; locate and track each target tracking signal according to the first preprocessing parameter and the second preprocessing parameter to obtain an initial ultrasound image; obtain image processing parameters, wherein the image processing parameters include image resolution, image contrast, image filtering and image enhancement; perform image processing on the initial ultrasound image according to the image processing parameters to obtain a target ultrasound image.

[0121] Each module in the aforementioned ultrasonic imaging device may be implemented in whole or in part through software, hardware, or a combination thereof. Each module may be embedded in or independent of a processor in a computer device in the form of hardware, or may be stored in a memory in the computer device in the form of software, so that the processor can call and execute the corresponding operations of each module.

[0122] In an exemplary embodiment, a computer device is provided, which may be a server, and its internal structure diagram may be shown in Figure 17. The computer device includes a processor, memory, an input / output (I / O) interface, and a communication interface. The processor, memory, and I / O interface are connected via a system bus, and the communication interface is connected to the system bus via the I / O interface. The processor of the computer device is used to provide computing and control capabilities. The memory of the computer device includes a non-volatile storage medium and an internal memory. The non-volatile storage medium stores an operating system, a computer program, and a database. The internal memory provides an environment for the operation of the operating system and computer program in the non-volatile storage medium. The database of the computer device is used to store ultrasound imaging data. The I / O interface of the computer device is used to exchange information between the processor and external devices. The communication interface of the computer device is used to communicate with external terminals via a network connection. When executed by the processor, the computer program implements an ultrasound imaging method.

[0123] In an exemplary embodiment, a computer device is provided. The computer device may be a terminal, and its internal structure may be shown in FIG18 . The computer device includes a processor, memory, an input / output interface, a communication interface, a display unit, and an input device. The processor, memory, and input / output interface are connected via a system bus, and the communication interface, display unit, and input device are connected to the system bus via the input / output interface. The processor of the computer device provides computing and control capabilities. The memory of the computer device includes a non-volatile storage medium and internal memory. The non-volatile storage medium stores an operating system and a computer program. The internal memory provides an environment for the operating system and computer program stored in the non-volatile storage medium. The input / output interface of the computer device is used to exchange information between the processor and external devices. The communication interface of the computer device is used to communicate with external terminals via wired or wireless communication, which may be achieved via Wi-Fi, a mobile cellular network, NFC (near-field communication), or other technologies. When executed by the processor, the computer program implements an ultrasound imaging method. The display unit of the computer device is used to produce a visual image and may be a display screen, a projection device, or a virtual reality imaging device. The display screen can be a liquid crystal display screen or an electronic ink display screen, and the input device of the computer device can be a touch layer covering the display screen, or a button, trackball or touchpad set on the computer device casing, or an external keyboard, touchpad or mouse.

[0124] Those skilled in the art will understand that the aforementioned structure is merely a block diagram of a portion of the structure related to the solution of the present application, and does not constitute a limitation on the computer device to which the solution of the present application is applied. The specific computer device may include more or fewer components than shown in the figure, or combine certain components, or have a different component arrangement.

[0125] In one embodiment, a computer device is provided, including a memory and a processor. The memory stores a computer program, and the processor implements the steps of the above method embodiments when executing the computer program.

[0126] In one embodiment, a computer-readable storage medium is provided, on which a computer program is stored. When the computer program is executed by a processor, the steps of the above-mentioned method embodiments are implemented.

[0127] In one embodiment, a computer program product is provided, including a computer program, which implements the steps of the above method embodiments when executed by a processor.

[0128] It should be noted that the user information (including but not limited to user device information, user personal information, etc.) and data (including but not limited to data used for analysis, stored data, displayed data, etc.) involved in this application are all information and data authorized by the user or fully authorized by all parties, and the collection, use and processing of relevant data must comply with relevant regulations.

[0129] Those skilled in the art will appreciate that all or part of the processes in the above-described method embodiments can be implemented by instructing the relevant hardware through a computer program. The computer program can be stored in a non-volatile computer-readable storage medium. When executed, the computer program can include the processes of the above-described method embodiments. Any reference to a memory, database, or other medium used in the embodiments provided herein may include at least one of non-volatile and volatile memory. Non-volatile memory may include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetic random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory may include random access memory (RAM) or external cache memory, etc. By way of illustration and not limitation, RAM can take various forms, such as static random access memory (SRAM) or dynamic random access memory (DRAM). The databases involved in the various embodiments provided herein may include at least one of a relational database and a non-relational database. Non-relational databases may include, but are not limited to, distributed databases based on blockchains. The processors involved in the various embodiments provided herein may be, but are not limited to, general-purpose processors, central processing units (CPUs), graphics processing units (GPUs), digital signal processors (DSPs), programmable logic devices (PLDs), data processing logic devices based on quantum computing, and the like.

[0130] The technical features of the above embodiments can be combined arbitrarily. To make the description concise, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0131] The above-described embodiments merely represent several implementation methods of the present application. While the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the present application. It should be noted that a person of ordinary skill in the art may make various modifications and improvements without departing from the spirit of the present application, and these modifications and improvements fall within the scope of protection of the present application. Therefore, the scope of protection of the present application shall be determined by the appended claims.

Claims

1. An ultrasonic imaging method, characterized in that: The method comprises: Acquiring an ultrasonic echo signal of a target area, wherein the ultrasonic echo signal is an echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area; Presetting a tracer substance in the target area, and determining a target imaging mode corresponding to the target area according to a magnitude relationship between the target emission frequency and a preset resonant frequency range of the tracer substance; Within a preset time period, the ultrasonic echo signal is collected according to the target imaging mode to obtain a plurality of target tracking signals, and each of the target tracking signals is located and tracked through the target imaging mode to obtain a target ultrasonic image.

2. The method according to claim 1, characterized in that The target imaging mode includes a two-dimensional fundamental wave imaging mode and a contrast imaging mode, and the target imaging mode corresponding to the target area is determined according to the magnitude relationship between the target emission frequency and the preset resonance frequency range of the tracer substance, including: When the target transmission frequency is not within the preset resonant frequency range, determining that the target imaging mode is the two-dimensional fundamental wave imaging mode, wherein the two-dimensional fundamental wave imaging mode performs ultrasonic imaging by collecting a two-dimensional fundamental wave signal in the ultrasonic echo signal; When the target transmission frequency is within the preset resonant frequency range, the target imaging mode is determined to be the contrast imaging mode, wherein the contrast imaging mode performs ultrasonic imaging by collecting contrast signals in the ultrasonic echo signals.

3. The method according to claim 2, characterized in that The two-dimensional fundamental wave signal includes a tissue signal and a first tracer signal, and the signal acquisition is performed on the ultrasonic echo signal according to the target imaging mode to obtain the target tracer signal, including: In the two-dimensional fundamental wave imaging mode, the ultrasonic echo signal is collected according to the two-dimensional fundamental wave imaging mode to obtain the two-dimensional fundamental wave signal; The two-dimensional fundamental wave signal is subjected to time-space filtering and frequency filtering respectively to filter out the tissue signal and obtain the first tracing signal.

4. The method according to claim 1, characterized in that: The method of collecting the ultrasonic echo signal according to the target imaging mode within the preset time period to obtain a plurality of target tracing signals includes: Within the preset time period, a plurality of initial tracer signals are obtained according to the movement of the tracer substance in the target area; Acquiring state parameters of each of the initial tracking signals, wherein the state parameters include position parameters, direction parameters and speed parameters; When the state parameter meets the preset parameter conditions, a plurality of target tracking signals are obtained.

5. The method according to claim 1, characterized in that Before acquiring the ultrasonic echo signal of the target area, the method includes: Acquire a first ultrasonic echo signal of a target object, where the first ultrasonic echo signal is an echo signal reflected after an ultrasonic signal is sent to the target object; A first ultrasonic image is obtained according to the first ultrasonic echo signal, and when a region of interest exists in the first ultrasonic image, the region of interest is used as the target region.

6. The method according to claim 5, characterized in that The step of processing the target tracing signal through the target imaging mode to obtain a target ultrasonic image includes: Acquire a first preprocessing parameter for controlling the number and intensity of bright spots in the ultrasound image, and a second preprocessing parameter for compensating for the motion of the target object; Positioning and tracking each of the target tracer signals according to the first preprocessing parameter and the second preprocessing parameter to obtain an initial ultrasonic image; Acquiring image processing parameters, wherein the image processing parameters include image resolution, image contrast, image filtering and image enhancement; The initial ultrasound image is processed according to the image processing parameters to obtain the target ultrasound image.

7. An ultrasonic imaging device, characterized in that: The device comprises: A receiving module, used to obtain an ultrasonic echo signal of a target area, wherein the ultrasonic echo signal is an echo signal reflected after an ultrasonic signal of a target transmission frequency is sent to the target area; An imaging mode determination module, used to preset a tracer substance in the target area, and determine a target imaging mode corresponding to the target area according to a magnitude relationship between the target emission frequency and a preset resonant frequency range of the tracer substance; The imaging module is used to collect the ultrasonic echo signal according to the target imaging mode within a preset time period to obtain multiple target tracking signals, and to locate and track each of the target tracking signals through the target imaging mode to obtain a target ultrasonic image.

8. A computer device comprising a memory and a processor, wherein the memory stores a computer program, wherein: When the processor executes the computer program, the steps of the method according to any one of claims 1 to 6 are implemented.

9. A computer-readable storage medium having a computer program stored thereon, characterized in that: When the computer program is executed by a processor, the steps of the method according to any one of claims 1 to 6 are implemented.

10. A computer program product, comprising a computer program, characterized in that When the computer program is executed by a processor, the steps of the method according to any one of claims 1 to 6 are implemented.

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