Ultrasonic attenuation compensation method and device, and electronic equipment

Abstract

The application provides an ultrasonic attenuation compensation method and device and electronic equipment, for each point of interest in an ultrasonic image, a sound channel is determined according to a plurality of ultrasonic transmitting elements arranged on an ultrasonic probe; for each sound channel, target data of each pixel point on the sound channel is obtained from the ultrasonic image; and according to the target data, an ultrasonic attenuation value for the point of interest is calculated to compensate ultrasonic energy emitted to the point of interest. According to the method, the sound channel is determined according to each point of interest in the ultrasonic image in combination with the ultrasonic transmitting elements, and then the ultrasonic attenuation value for the point of interest is determined according to the target data such as the gray value and TGC value of each pixel point on the sound channel. Since the target data of different pixel points can reflect the heterogeneity of the acoustic impedance of different individuals, the accuracy of the obtained ultrasonic attenuation value can be improved, and the accuracy of the compensation of the ultrasonic energy is improved.

Description

Technical Field

[0001] This invention relates to the field of ultrasonic technology, and in particular to an ultrasonic attenuation compensation method, device, and electronic device. Background Technology

[0002] Ultrasound energy attenuates with increasing transmission distance in a medium. To achieve precise delivery of ultrasound energy within the body, ultrasound energy therapy devices require accurate compensation for this attenuation. Traditional compensation techniques calculate the acoustic channel length by measuring the distance from the target location (i.e., the point where energy needs to be projected) to the skin surface. This length is then multiplied by the average attenuation coefficient of human tissue reported in relevant literature to calculate the total ultrasound attenuation of the acoustic channel. Compensation is then applied based on this total attenuation to increase the ultrasound energy emitted by the array elements, ensuring that the attenuated ultrasound energy reaches the required level at the target location. However, this method ignores the heterogeneity of tissue acoustic impedance among different individuals. The actual average attenuation coefficient of human tissue will deviate from the average attenuation coefficient reported in the literature, leading to inaccurate compensation of ultrasound energy. Summary of the Invention

[0003] The purpose of this invention is to provide an ultrasonic attenuation compensation method, device, and electronic device to improve the accuracy of ultrasonic energy compensation.

[0004] This invention provides an ultrasound attenuation compensation method, comprising: acquiring an ultrasound image containing a lesion site using an ultrasound probe; wherein the ultrasound image contains a region of interest; the region of interest is a region containing at least a portion of the lesion site; the region of interest includes multiple points of interest; for each point of interest, determining an acoustic channel between each ultrasound transmitting element and the point of interest based on multiple ultrasound transmitting elements arranged on the ultrasound probe; for each acoustic channel, acquiring target data for each pixel in the acoustic channel from the ultrasound image; wherein the target data includes: grayscale value and TGC value; and calculating an ultrasound attenuation value for the point of interest based on the target data for each pixel in the acoustic channel, so as to compensate the ultrasound energy emitted to the point of interest based on the ultrasound attenuation value.

[0005] Furthermore, the step of calculating the ultrasonic attenuation value for the point of interest based on the target data of each pixel in the acoustic channel includes: calculating the first attenuation value corresponding to the acoustic channel based on the target data of each pixel in the acoustic channel; and weighting and averaging the first attenuation values ​​corresponding to each acoustic channel to obtain the ultrasonic attenuation value for the point of interest.

[0006] Furthermore, the step of calculating the first attenuation value corresponding to the sound channel based on the target data of each pixel in the sound channel includes: calculating a first parameter value for each pixel in the sound channel based on the target data of the pixel; integrating the first parameter value of each pixel in the sound channel to obtain an integration result; calculating the product of the integration result and a preset adjustment coefficient to obtain a product result; calculating a calculation result with a preset value as the base and the product result as the exponent, and determining the calculation result as the first attenuation value corresponding to the sound channel.

[0007] Furthermore, the first parameter value is positively correlated with the grayscale value in the target data and negatively correlated with the TGC value in the target data.

[0008] Furthermore, the target data also includes: LGC value.

[0009] Furthermore, the ultrasound images are either 2D or 3D images.

[0010] This invention provides an ultrasound attenuation compensation device, comprising: an acquisition module for acquiring an ultrasound image containing a lesion site via an ultrasound probe; wherein the ultrasound image contains a region of interest; the region of interest is a region containing at least a portion of the lesion site; the region of interest includes multiple points of interest; a determination module for determining, for each point of interest, an acoustic channel between each ultrasound transmitting element and the point of interest based on multiple ultrasound transmitting elements arranged on the ultrasound probe; an acquisition module for acquiring, for each acoustic channel, target data of each pixel in the ultrasound image; wherein the target data includes: grayscale value and TGC value; and a calculation module for calculating an ultrasound attenuation value for the point of interest based on the target data of each pixel in the acoustic channel, so as to compensate the ultrasound energy emitted to the point of interest based on the ultrasound attenuation value.

[0011] Furthermore, the calculation module is also used to: calculate the first attenuation value corresponding to the sound channel based on the target data of each pixel point on the sound channel; and to perform a weighted average of the first attenuation values ​​corresponding to each sound channel to obtain the ultrasonic attenuation value for the point of interest.

[0012] The present invention provides an electronic device, including a processor and a memory, wherein the memory stores machine-executable instructions that can be executed by the processor, and the processor executes the machine-executable instructions to implement the ultrasonic attenuation compensation method described above.

[0013] The present invention provides a machine-readable storage medium storing machine-executable instructions, which, when called and executed by a processor, cause the processor to implement any of the above-mentioned ultrasonic attenuation compensation methods.

[0014] The ultrasonic attenuation compensation method, apparatus, and electronic device provided by this invention acquire an ultrasonic image containing a lesion site using an ultrasonic probe. The ultrasonic image includes a region of interest (ROI). The ROI is a region containing at least a portion of the lesion site. The ROI includes multiple points of interest (POIs). For each POI, an acoustic channel is determined between each ultrasonic transmitting element and the POI based on multiple ultrasonic transmitting elements arranged on the ultrasonic probe. For each acoustic channel, target data for each pixel on the acoustic channel is acquired from the ultrasonic image. The target data includes grayscale values ​​and TGC values. Based on the target data for each pixel on the acoustic channel, an ultrasonic attenuation value is calculated for the POI to compensate for the ultrasonic energy emitted towards the POI. This method determines the acoustic channel based on each point of interest in the ultrasound image and the ultrasound transmission array elements. Then, based on the target data such as the gray value and TGC value of each pixel in the acoustic channel, the ultrasound attenuation value for the point of interest is determined. Since the target data of different pixels can reflect the heterogeneity of tissue acoustic impedance in different individuals, the accuracy of the obtained ultrasound attenuation value can be improved, thereby improving the accuracy of ultrasound energy compensation. Attached Figure Description

[0015] To more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0016] Figure 1 A flowchart of an ultrasonic attenuation compensation method provided in an embodiment of the present invention; Figure 2 A schematic diagram of an acoustic channel provided in an embodiment of the present invention; Figure 3 A schematic diagram of another acoustic channel provided in an embodiment of the present invention; Figure 4 A flowchart of another ultrasonic attenuation compensation method provided in an embodiment of the present invention; Figure 5 This is a schematic diagram of the structure of an ultrasonic attenuation compensation device provided in an embodiment of the present invention; Figure 6 This is a schematic diagram of the structure of an electronic device provided in an embodiment of the present invention. Detailed Implementation

[0017] The technical solution of the present invention will be clearly and completely described below with reference to the embodiments. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0018] In order to achieve precise delivery of ultrasound energy within the body, ultrasound energy therapy devices require proper compensation for ultrasound attenuation. Correct compensation is crucial for treatment; excessive compensation can lead to excessive energy projection, causing complications such as damage to normal tissues. Insufficient compensation, on the other hand, results in insufficient energy projection, failing to achieve the intended therapeutic effect.

[0019] Traditional compensation techniques calculate the length of the acoustic channel by measuring the distance from the target location (the location where energy needs to be projected) to the skin surface, then multiply it by the average human tissue attenuation coefficient reported in the literature to calculate the total ultrasound attenuation of the acoustic channel. Finally, compensation is performed based on this total ultrasound attenuation to increase the ultrasound energy emitted by the array elements in reverse, so that the ultrasound energy after attenuation reaches the required energy level at the target location.

[0020] However, traditional compensation methods use the average attenuation coefficient of human tissue reported in the literature, ignoring the heterogeneity of tissue acoustic impedance among different individuals. For example, the composition of tissues in the sound propagation path, the ratio of muscle to fat, scattering at tissue interfaces, heat generation, the presence of gas, fibrous tissue, and differences in patient size can all cause the actual average attenuation coefficient of human tissue to deviate from the average attenuation coefficient of human tissue reported in the literature. This leads to inaccurate calculation of the total ultrasound attenuation and inaccurate compensation of ultrasound energy.

[0021] To facilitate understanding of this embodiment, an ultrasonic attenuation compensation method disclosed in this embodiment of the invention will first be introduced, such as... Figure 1 As shown, the method includes the following steps: Step S102: Acquire an ultrasound image containing the lesion site using an ultrasound probe; wherein the ultrasound image contains a region of interest; the region of interest is: a region containing at least a portion of the lesion site; the region of interest includes multiple points of interest; The aforementioned lesion site can be understood as the specific location of a disease or abnormality in the human body; a region of interest can be selected in the ultrasound image according to actual needs. This region of interest can include a part of the lesion site or the entire lesion site; the aforementioned point of interest can be a single pixel or a region composed of multiple adjacent pixels, which can be set according to actual needs and is not limited here; in actual implementation, the ultrasound image containing the lesion site can be acquired by an ultrasound probe.

[0022] Step S104: For each point of interest, determine the acoustic channel between each ultrasonic transmitting element and the point of interest based on the multiple ultrasonic transmitting elements arranged on the ultrasonic probe. The aforementioned ultrasonic transmitting elements can be used to emit ultrasonic energy. In actual implementation, multiple ultrasonic transmitting elements are usually arranged on the ultrasonic probe. The layout of these multiple ultrasonic transmitting elements can be set according to actual needs, such as a ring layout, a matrix layout, etc. In actual implementation, for each point of interest, based on the position of the point of interest and the layout of the multiple ultrasonic transmitting elements, the acoustic channel between each ultrasonic transmitting element and the point of interest is determined. This acoustic channel can be understood as the line connecting the point of interest to each ultrasonic transmitting element. It can be understood that the number of ultrasonic transmitting elements is the same as the number of acoustic channels.

[0023] Step S106: For each acoustic channel, acquire the target data of each pixel in that acoustic channel from the ultrasound image; wherein, the target data includes: gray value and TGC value; The grayscale values ​​mentioned above can be used to represent the brightness of a pixel. A higher grayscale value indicates a brighter pixel, and a lower grayscale value indicates a darker pixel. The TGC (Time Gain Compensation) value refers to the gain compensation value of the echo signal at different depth positions in the image. By obtaining the TGC value of each pixel, depth compensation can be performed on each pixel to eliminate the difference in echo signal attenuation caused by different sound wave propagation distances. The aforementioned acoustic channel refers to the path and channel through which ultrasound waves propagate in human tissue. One acoustic channel typically corresponds to multiple pixels. In actual implementation, for each acoustic channel, target data such as the grayscale value and TGC value of each pixel in that acoustic channel can be extracted from the ultrasound image.

[0024] Step S108: Calculate the ultrasonic attenuation value for the point of interest based on the target data of each pixel in the acoustic channel, so as to compensate the ultrasonic energy emitted to the point of interest based on the ultrasonic attenuation value.

[0025] The aforementioned ultrasonic attenuation value represents the overall attenuation of ultrasonic energy when it is emitted towards the point of interest. The larger the ultrasonic attenuation value, the greater the overall attenuation of ultrasonic energy; the smaller the ultrasonic attenuation value, the less the overall attenuation of ultrasonic energy. In actual implementation, after acquiring the target data of each pixel in the acoustic channel, the overall ultrasonic attenuation value of the point of interest can be calculated based on the target data of each pixel. Then, the ultrasonic energy emitted towards the point of interest can be compensated according to the ultrasonic attenuation value, so that the ultrasonic energy reaching the point of interest can reach the required energy level.

[0026] The aforementioned ultrasound attenuation compensation method involves acquiring an ultrasound image containing the lesion site using an ultrasound probe. The ultrasound image includes a region of interest (ROI), which is a region containing at least a portion of the lesion site. The ROI includes multiple points of interest (POIs). For each POI, an acoustic channel is determined between each ultrasound transmitter element and the POI based on multiple ultrasound transmitter elements arranged on the ultrasound probe. For each acoustic channel, target data for each pixel in the acoustic channel is acquired from the ultrasound image. The target data includes grayscale value and TGC value. Based on the target data for each pixel in the acoustic channel, an ultrasound attenuation value is calculated for the POI, and this attenuation value is used to compensate for the ultrasound energy emitted towards the POI. This method determines the acoustic channel based on each POI in the ultrasound image and the ultrasound transmitter elements, and then determines the ultrasound attenuation value for the POI based on the target data such as the grayscale value and TGC value of each pixel in the acoustic channel. Since the target data for different pixels can reflect the heterogeneity of tissue acoustic impedance in different individuals, the accuracy of the obtained ultrasound attenuation value can be improved, thereby improving the accuracy of ultrasound energy compensation.

[0027] This invention also provides another ultrasonic attenuation compensation method, which is implemented based on the method in the above embodiments, and includes the following steps: Step 1: Acquire ultrasound images containing the lesion site using an ultrasound probe; wherein, the ultrasound image contains a region of interest; the region of interest is: a region containing at least a portion of the lesion site; the region of interest includes multiple points of interest; The ultrasound images mentioned above can be 2D or 3D images; the 2D image is a planar image with only length and width information; the 3D image is a three-dimensional image reconstructed by computer based on the 2D image, and has length, width and depth information.

[0028] Step 2: For each point of interest, determine the acoustic channel between each ultrasonic transmitting element and the point of interest based on the multiple ultrasonic transmitting elements arranged on the ultrasonic probe. For example, such as Figure 2 The diagram shown represents a sound channel in a three-dimensional mode. In this mode, a 3D ultrasound image can be obtained by rotating the ultrasound probe (the method of acquiring the 3D ultrasound image can be set according to actual needs and is not limited here). Then, lines are drawn from the position of each ultrasound transmitting element to the point of interest to obtain the sound channel. Figure 2 In the diagram, point 1 represents the point of interest, point 2 represents the location where the ultrasound waves hit the skin surface, and point 3 represents the ultrasound emission element. For example... Figure 3 The diagram shows another acoustic channel, which corresponds to a two-dimensional mode. In the two-dimensional mode, a 2D ultrasound image can be obtained through an ultrasound probe. Lines can be drawn from each ultrasound transmitting element to the point of interest to obtain the acoustic channel corresponding to each ultrasound transmitting element.

[0029] Step 3: For each acoustic channel, acquire the target data of each pixel in that acoustic channel from the ultrasound image; the target data includes: grayscale value and TGC value. Step 4: Calculate the first attenuation value corresponding to the sound channel based on the target data of each pixel in the sound channel; This fourth step can be achieved through the following steps 40 to 42: Step 40: For each pixel in the sound channel, calculate the first parameter value based on the target data of that pixel; In practical implementation, the first parameter value can be calculated for each pixel in the audio channel based on the pixel's grayscale value, TGC value, and other target data. For example, using... Represents pixels grayscale value at that location Represents pixels The TGC value at that location; can be used as Indicates the value of the first parameter. This can represent the contribution of each pixel to the decay. Received and The first parameter value is usually positively correlated with the grayscale value in the target data and negatively correlated with the TGC value in the target data. The specific calculation method of the first parameter value can be set according to actual needs and is not limited here.

[0030] In one embodiment, the target data further includes an LGC (Lateral Gain Compensation) value, which can be used to compensate for signal intensity differences in the lateral direction of the ultrasound probe; in this case, it can be used in the above... Add LGC(x, y) as a parameter for adjustment, where LGC(x, y) represents the pixel value. The LGC value at that location is negatively correlated with the LGC value.

[0031] Step 41: Integrate the first parameter value of each pixel in the audio channel to obtain the integration result; Step 42: Calculate the product of the integral processing result and the preset adjustment coefficient to obtain the product result; Step 43: Calculate the result with a preset value as the base and the product result as the exponent, and determine the calculation result as the first attenuation value corresponding to the sound channel; In practical implementation, the sound channel can be integrally processed based on the first parameter value of each pixel. The integral result is then multiplied by a preset adjustment coefficient to obtain the product. The preset adjustment coefficient can be set according to actual needs. For example, the preset adjustment coefficient can be set to... This indicates that the first parameter value is... This indicates that, due to the preset adjustment coefficient, It is usually a preset constant value, therefore, The result of the product can be expressed either within or outside the integral sign; therefore, the product result can be represented as... .

[0032] After obtaining the product result, the corresponding first attenuation value can be calculated using a preset value as the base and the product result as the exponent. For example, if the preset value is 10, the first attenuation value can be calculated using... This means that the integration starting point of the acoustic channel is the transmitting element (i.e., the ultrasonic transmitting element mentioned above), and the integration ending point is the focal point, i.e., the predetermined energy projection position (corresponding to the point of interest mentioned above).

[0033] Step 5: Take a weighted average of the first attenuation values ​​corresponding to each acoustic channel to obtain the ultrasonic attenuation value for the point of interest, so as to compensate the ultrasonic energy emitted to the point of interest based on the ultrasonic attenuation value.

[0034] For example, continuing with the above embodiment, assuming the number of acoustic channels is represented by n, it can be understood that the number of ultrasonic transmitting elements is also n. Therefore, the ultrasonic attenuation value for the point of interest can be expressed as: Where g(n) represents the weight of the nth ultrasonic transmitting element, and the weight is proportional to the relative energy of the ultrasonic transmitting element; that is, the higher the ultrasonic energy emitted by the ultrasonic transmitting element, the greater its corresponding weight. The ultrasonic energy emitted towards the point of interest can be compensated according to this ultrasonic attenuation value, so that the ultrasonic energy finally reaching the point of interest can reach the required energy level.

[0035] In another embodiment, the approach can be extended to the time dimension, where the ultrasound image changes over time. This allows the attenuation calculated using grayscale values ​​to be averaged over time, making it more suitable for long-term treatment (avoiding interference from respiratory movements). In this case, the ultrasound attenuation value can be understood as the weighted average attenuation value at the current moment. Multiple weighted average attenuation values ​​at different time points can be taken, and then the average can be taken to obtain the final ultrasound energy that needs to be compensated.

[0036] For ease of understanding, see Figure 4 The flowchart of another ultrasonic attenuation compensation method shows that, firstly, an ultrasonic image is acquired. For each point of interest in the ultrasonic image, the acoustic channel between each ultrasonic transmitting element and the point of interest is determined based on the layout of the ultrasonic transmitting elements. For each acoustic channel, the grayscale value and TGC value of each pixel in the acoustic channel are obtained from the ultrasonic image. The first attenuation value of each acoustic channel is calculated according to a preset calculation method. After weighted averaging based on the first attenuation value of each acoustic channel, the ultrasonic attenuation value is obtained. The ultrasonic attenuation value is used to compensate for the ultrasonic energy so that the ultrasonic energy finally reaching the point of interest can reach the required energy level.

[0037] The aforementioned ultrasound attenuation compensation method locates the point of interest in an ultrasound image, and combines this with target data such as the grayscale value and TGC value of each pixel in the ultrasound image to obtain tissue acoustic impedance information. It then obtains the first attenuation value for each acoustic path through integration, and finally calculates a weighted average of these first attenuation values ​​to obtain the ultrasound attenuation value for that point of interest. This method overcomes the problem of previous techniques neglecting the heterogeneity of tissue acoustic impedance, thereby improving the accuracy of ultrasound energy compensation.

[0038] This invention provides an ultrasonic attenuation compensation device, such as... Figure 5 As shown, the device includes: an acquisition module 50, used to acquire ultrasound images containing lesion sites via an ultrasound probe; wherein the ultrasound image contains a region of interest; the region of interest is a region containing at least a portion of the lesion site; the region of interest includes multiple points of interest; a determination module 51, used to determine the acoustic channel between each ultrasound transmitting element and the point of interest based on multiple ultrasound transmitting elements arranged on the ultrasound probe for each point of interest; an acquisition module 52, used to acquire target data of each pixel on the acoustic channel from the ultrasound image for each acoustic channel; wherein the target data includes: grayscale value and TGC value; and a calculation module 53, used to calculate the ultrasound attenuation value for the point of interest based on the target data of each pixel on the acoustic channel, so as to compensate the ultrasound energy emitted to the point of interest based on the ultrasound attenuation value.

[0039] The aforementioned ultrasonic attenuation compensation device determines the acoustic channel based on each point of interest in the ultrasonic image and the ultrasonic transmitting array elements. Then, based on the target data such as the gray value and TGC value of each pixel in the acoustic channel, it determines the ultrasonic attenuation value for the point of interest. Since the target data of different pixels can reflect the heterogeneity of the acoustic impedance of tissues in different individuals, the accuracy of the obtained ultrasonic attenuation value can be improved, thereby improving the accuracy of ultrasonic energy compensation.

[0040] Furthermore, the calculation module is also used to: calculate the first attenuation value corresponding to the sound channel based on the target data of each pixel point on the sound channel; and to perform a weighted average of the first attenuation values ​​corresponding to each sound channel to obtain the ultrasonic attenuation value for the point of interest.

[0041] Furthermore, the calculation module is also used to: calculate a first parameter value for each pixel in the sound channel based on the target data of the pixel; integrate the first parameter value of each pixel in the sound channel to obtain an integration result; calculate the product of the integration result and a preset adjustment coefficient to obtain a product result; calculate the calculation result with the preset value as the base and the product result as the exponent, and determine the calculation result as the first attenuation value corresponding to the sound channel.

[0042] Furthermore, the first parameter value is positively correlated with the grayscale value in the target data and negatively correlated with the TGC value in the target data.

[0043] Furthermore, the target data also includes: LGC value.

[0044] Furthermore, the ultrasound images are either 2D or 3D images.

[0045] The ultrasonic attenuation compensation device provided in this embodiment of the invention has the same implementation principle and technical effect as the aforementioned ultrasonic attenuation compensation method embodiment. For the sake of brevity, any parts not mentioned in the ultrasonic attenuation compensation device embodiment can be referred to the corresponding content in the aforementioned ultrasonic attenuation compensation method embodiment.

[0046] This invention also provides an electronic device, see [link to relevant documentation]. Figure 6 As shown, the electronic device includes a processor 130 and a memory 131. The memory 131 stores machine-executable instructions that can be executed by the processor 130. The processor 130 executes the machine-executable instructions to implement the ultrasonic attenuation compensation method described above.

[0047] Furthermore, Figure 6 The electronic device shown also includes a bus 132 and a communication interface 133, with the processor 130, the communication interface 133 and the memory 131 connected via the bus 132.

[0048] The memory 131 may include high-speed random access memory (RAM) and may also include non-volatile memory, such as at least one disk storage device. Communication between this system network element and at least one other network element is achieved through at least one communication interface 133 (which can be wired or wireless), such as the Internet, wide area network, local area network, metropolitan area network, etc. The bus 132 may be an ISA bus, PCI bus, or EISA bus, etc. The bus can be divided into address bus, data bus, control bus, etc. For ease of representation, Figure 6 The symbol is represented by a single double-headed arrow, but this does not mean that there is only one bus or one type of bus.

[0049] Processor 130 may be an integrated circuit chip with signal processing capabilities. In implementation, each step of the above method can be completed by the integrated logic circuitry in the hardware of processor 130 or by instructions in software form. Processor 130 may be a general-purpose processor, including a Central Processing Unit (CPU), a Network Processor (NP), etc.; it may also be a Digital Signal Processor (DSP), an Application Specific Integrated Circuit (ASIC), a Field-Programmable Gate Array (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, or discrete hardware components. It can implement or execute the methods, steps, and logic block diagrams disclosed in the embodiments of this invention. The general-purpose processor may be a microprocessor or any conventional processor. The steps of the methods disclosed in the embodiments of this invention can be directly manifested as execution by a hardware decoding processor, or execution by a combination of hardware and software modules in the decoding processor. The software module can reside in a mature storage medium in the art, such as random access memory, flash memory, read-only memory, programmable read-only memory, electrically erasable programmable memory, or registers. This storage medium is located in memory 131, and processor 130 reads the information in memory 131 and, in conjunction with its hardware, completes the steps of the method described in the foregoing embodiments.

[0050] This invention also provides a machine-readable storage medium storing machine-executable instructions. When these machine-executable instructions are called and executed by a processor, they cause the processor to implement the aforementioned ultrasonic attenuation compensation method. For specific implementation details, please refer to the method embodiments, which will not be repeated here.

[0051] The computer program product of the ultrasonic attenuation compensation method, device and electronic device provided in the embodiments of the present invention includes a computer-readable storage medium storing program code. The instructions included in the program code can be used to execute the methods described in the preceding method embodiments. For specific implementation, please refer to the method embodiments, which will not be repeated here.

[0052] If the aforementioned functions are implemented as software functional units and sold or used as independent products, they can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this invention, essentially, or the part that contributes to the prior art, or a portion of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of this invention. The aforementioned storage medium includes various media capable of storing program code, such as USB flash drives, portable hard drives, read-only memory (ROM), random access memory (RAM), magnetic disks, or optical disks.

[0053] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some or all of the technical features therein. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims

1. A method for ultrasonic attenuation compensation, characterized in that, The method includes: An ultrasound image containing the lesion site is acquired using an ultrasound probe; wherein the ultrasound image contains a region of interest; the region of interest is a region containing at least a portion of the lesion site; the region of interest includes multiple points of interest. For each point of interest, the acoustic channel between each ultrasonic transmitting element and the point of interest is determined based on the multiple ultrasonic transmitting elements arranged on the ultrasonic probe. For each of the aforementioned acoustic channels, target data for each pixel in that acoustic channel is acquired from the ultrasound image; wherein, the target data includes: grayscale value and TGC value; Based on the target data of each pixel in the acoustic channel, an ultrasonic attenuation value is calculated for the point of interest, so as to compensate for the ultrasonic energy emitted toward the point of interest according to the ultrasonic attenuation value.

2. The method according to claim 1, characterized in that, The step of calculating the ultrasonic attenuation value for the point of interest based on the target data of each pixel in the acoustic channel includes: Calculate the first attenuation value corresponding to the sound channel based on the target data of each pixel in the sound channel; The first attenuation value corresponding to each acoustic channel is weighted and averaged to obtain the ultrasonic attenuation value for the point of interest.

3. The method according to claim 2, characterized in that, The step of calculating the first attenuation value corresponding to the sound channel based on the target data of each pixel in the sound channel includes: For each pixel in the audio channel, calculate the first parameter value based on the target data of that pixel; The first parameter value of each pixel in the audio channel is integrated to obtain the integration result. Calculate the product of the integral processing result and the preset adjustment coefficient to obtain the product result; The calculation is performed with a preset value as the base and the product result as the exponent. The calculated result is then determined as the first attenuation value corresponding to the sound channel.

4. The method according to claim 3, characterized in that, The first parameter value is positively correlated with the grayscale value in the target data and negatively correlated with the TGC value in the target data.

5. The method according to claim 2, characterized in that, The target data also includes: LGC value.

6. The method according to claim 1, characterized in that, The ultrasound image is a 2D image or a 3D image.

7. An ultrasonic attenuation compensation device, characterized in that, The device includes: An acquisition module is used to acquire ultrasound images containing lesion sites via an ultrasound probe; wherein the ultrasound images contain a region of interest; the region of interest is a region containing at least a portion of the lesion site; the region of interest includes multiple points of interest. The determination module is used to determine the acoustic channel between each ultrasonic transmitting element and the point of interest, based on the multiple ultrasonic transmitting elements arranged on the ultrasonic probe, for each point of interest. The acquisition module is used to acquire target data of each pixel in each of the acoustic channels from the ultrasound image; wherein the target data includes: grayscale value and TGC value; The calculation module is used to calculate the ultrasonic attenuation value for the point of interest based on the target data of each pixel on the acoustic channel, so as to compensate the ultrasonic energy emitted to the point of interest based on the ultrasonic attenuation value.

8. The apparatus according to claim 7, characterized in that, The computing module is also used for: Calculate the first attenuation value corresponding to the sound channel based on the target data of each pixel in the sound channel; The first attenuation value corresponding to each acoustic channel is weighted and averaged to obtain the ultrasonic attenuation value for the point of interest.

9. An electronic device, characterized in that, It includes a processor and a memory, the memory storing machine-executable instructions that can be executed by the processor, the processor executing the machine-executable instructions to implement the ultrasonic attenuation compensation method according to any one of claims 1-6.

10. A machine-readable storage medium, characterized in that, The machine-readable storage medium stores machine-executable instructions that, when invoked and executed by a processor, cause the processor to implement the ultrasonic attenuation compensation method according to any one of claims 1-6.

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