Bone mineral density measuring method, device and equipment and storage medium

Abstract

The invention relates to a bone mineral density measuring method and device, equipment and a storage medium. According to the scheme, when the bone mineral density is measured, firstly, an original medical image is obtained, and image processing operation including scattering correction processing operation is executed on the original medical image, so that scattering components of the original medical image are removed by simulating scattering distribution through the scattering correction processing operation; and then determining a first attenuation image by using the target medical image and the air image, and determining a bone mineral density value according to the first attenuation image and a bone mineral density calculation rule. Therefore, when the bone mineral density is measured, extra hardware such as a bone mineral density standard body and a scattering correction lead plate does not need to be used, only the high-energy original medical image and the low-energy original medical image need to be obtained, and image processing operation including scattering correction processing operation is executed on the images, so that scattering components can be effectively removed; and the bone mineral density measurement speed and accuracy are improved.

Description

Technical Field

[0001] The present application relates to the field of medical image processing technology, and in particular to a bone density measurement method, device, equipment and storage medium. Background Art

[0002] Osteoporosis is a metabolic bone disease, which is mainly caused by bone loss and reduced bone strength, destruction of bone tissue microstructure, and increased bone brittleness, which makes patients prone to fractures. Therefore, rapid and accurate measurement of human bone density is of great significance for the diagnosis and prevention of osteoporosis. At present, the measurement of bone density mainly relies on dedicated pencil beam or fan beam dual energy X-ray absorptiometry (Dule Energy X-Ray Absorptiometry, DEXA) and digital X-ray photography system (Digital Radiography, DR) to measure bone density. However, the scanning speed of DEXA's pencil beam scanning method is very slow, and the fan beam scanning method reduces the accuracy of the measured bone density value due to scattering. DR requires the use of a standard body for reference, or the use of a dedicated scatter correction lead plate, and requires the acquisition of four images of the patient, which complicates the acquisition process and cannot accurately measure bone density for complex parts.

[0003] Therefore, how to measure bone density more quickly and accurately is a problem that technicians in this field need to solve. Summary of the invention

[0004] The present application provides a bone density measurement method, device, equipment and storage medium to measure bone density more quickly and accurately.

[0005] In a first aspect, the present application provides a method for measuring bone density, comprising:

[0006] Acquire an original medical image; wherein the original medical image includes a high-energy original medical image and a low-energy original medical image;

[0007] Performing an image processing operation on the original medical image to obtain a target medical image; the image processing operation includes a scatter correction processing operation, wherein the scatter correction processing operation removes the scatter component of the original medical image by simulating scatter distribution;

[0008] Determine a first attenuation image using the target medical image and the air image; wherein the air image includes a high-energy air image and a low-energy air image, and the first attenuation image includes a first high-energy attenuation image and a first low-energy attenuation image;

[0009] A bone density value is determined according to the first attenuation image and a bone density calculation rule.

[0010] Optionally, the scatter correction processing operation includes:

[0011] Determine a second attenuation image using the image to be processed and the air image, and use the second attenuation image as the initial image; wherein the image to be processed is an image that needs to perform a scatter correction processing operation;

[0012] Determine the equivalent water thickness of each pixel in the initial image;

[0013] Determine the scattering kernel of each pixel point according to the equivalent water thickness of each pixel point;

[0014] Superimposing the scattering kernel of each pixel point with the initial image to obtain a first scattering distribution image; wherein the scattering distribution image of the current cycle is the first scattering distribution image, and the scattering distribution image of the previous cycle is the second scattering distribution image;

[0015] If the difference between the first scattering distribution image and the second scattering distribution image is less than a predetermined threshold, a main light image is calculated according to the second attenuation image and the first scattering distribution image, and the main light image is used as a scattering correction processing result;

[0016] If the second scattering distribution image does not exist, or the difference between the first scattering distribution image and the second scattering distribution image is not less than a predetermined threshold, the main light image is calculated according to the second attenuation image and the first scattering distribution image, and the main light image is used as the initial image, and the step of determining the equivalent water thickness of each pixel in the initial image is continued.

[0017] Optionally, taking the second attenuation image as the initial image comprises:

[0018] performing downsampling processing on the second attenuated image to obtain a downsampled image;

[0019] Using the downsampled image as an initial image;

[0020] Correspondingly, superimposing the scattering kernel of each pixel point with the initial image to obtain the first scattering distribution image includes:

[0021] The scattering kernel of each pixel point is superimposed with the initial image to obtain a superimposed image;

[0022] performing upsampling processing on the superimposed image to obtain a first scattering distribution image;

[0023] Accordingly, the main light image is used as the initial image, including:

[0024] The main light image is downsampled to obtain a downsampled main light image, and the downsampled main light image is used as the initial image.

[0025] Optionally, acquiring the original medical image includes:

[0026] An original medical image is acquired through a digital X-ray photography system; wherein the original medical image is an image generated after scattering processing is performed through a grid filter.

[0027] Optionally, performing an image processing operation on the original medical image to obtain a target medical image includes:

[0028] A flat panel correction processing operation, a bad channel correction processing operation, an overexposure correction processing operation, a scatter correction processing operation and a noise reduction processing operation are performed on the original medical image to obtain a target medical image; wherein the target medical image includes: a high-energy target medical image and a low-energy target medical image.

[0029] Optionally, determining a first attenuation image using the target medical image and the air image includes:

[0030] Segmenting the region of interest image in the target medical image; wherein the region of interest image includes: a high-energy region of interest image and a low-energy region of interest image;

[0031] A first attenuation image is determined using the region of interest image and the air image.

[0032] Optionally, after acquiring the original medical image, the method further includes:

[0033] Determining an actual mAs value of the original medical image;

[0034] The air image is obtained by fitting the pre-collected initial air image; the mAs value of the air image is the same as the actual mAs value.

[0035] Optionally, determining the bone density value according to the first attenuation image and a bone density calculation rule includes:

[0036] Inputting the first attenuation image into a bone density calculation rule to determine a bone density value;

[0037] The bone density calculation rule is:

[0038] bmd(x,y)=p00+p10*x+p01*y+p20*x 2 +p11*x*y+

[0039] p02*y 2 +p21*x 2 *y+p12*x*y 2 +p03*y 3 +p22*x 2 *y 2 +p13*x*y 3+p04*y 4 +p23*x 2 *y 3 +p14*x*y 4 +p05*y 5 ;

[0040] Among them, bmd is the bone density value, x is the first high-energy attenuation image, y is the first low-energy attenuation image, p00 is the first coefficient, p10 is the second coefficient, p01 is the third coefficient, p20 is the fourth coefficient, p11 is the fifth coefficient, p02 is the sixth coefficient, p21 is the seventh coefficient, p12 is the eighth coefficient, p03 is the ninth coefficient, p22 is the tenth coefficient, p13 is the eleventh coefficient, p04 is the twelfth coefficient, p23 is the thirteenth coefficient, p14 is the fourteenth coefficient, and p05 is the fifteenth coefficient.

[0041] In a second aspect, the present application provides a bone density measuring device, comprising:

[0042] An acquisition module, used for acquiring original medical images; wherein the original medical images include high-energy original medical images and low-energy original medical images;

[0043] A processing module, configured to perform an image processing operation on the original medical image to obtain a target medical image; the image processing operation includes a scatter correction processing operation, wherein the scatter correction processing operation removes the scatter component of the original medical image by simulating scatter distribution;

[0044] A first determination module, configured to determine a first attenuation image using the target medical image and the air image; wherein the air image includes a high-energy air image and a low-energy air image, and the first attenuation image includes a first high-energy attenuation image and a first low-energy attenuation image;

[0045] The second determination module is used to determine the bone density value according to the first attenuation image and the bone density calculation rule.

[0046] In a third aspect, the present application provides an electronic device, including:

[0047] A processor, a memory, and a computer program stored in the memory and executable on the processor, wherein the processor executes the steps of the above-mentioned bone density measurement method of the present application through the computer program.

[0048] In a fourth aspect, the present application further provides a computer storage medium, wherein the computer storage medium stores computer executable instructions, and the computer executable instructions are used to execute the steps of the above-mentioned bone density measurement method of the present application.

[0049] The above technical solution provided by the embodiment of the present application has the following advantages over the prior art: the present application provides a bone density measurement solution, the present solution obtains the original medical image, performs image processing operations including scatter correction processing operations on the original medical image, so as to remove the scattering components of the original medical image by simulating the scattering distribution through the scatter correction processing operation; then the first attenuation image is determined using the target medical image and the air image, and the bone density value is determined according to the first attenuation image and the bone density calculation rule. It can be seen that when measuring bone density, the present application does not need to use additional hardware such as bone density standards and scatter correction lead plates, but only needs to obtain high-energy original medical images and low-energy original medical images, and perform image processing operations including scatter correction processing operations on them, so as to effectively remove the scattering components and improve the speed and accuracy of bone density measurement. BRIEF DESCRIPTION OF THE DRAWINGS

[0050] The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the invention and, together with the description, serve to explain the principles of the invention.

[0051] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, for ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative labor.

[0052] One or more embodiments are exemplarily described by pictures in the corresponding drawings, and these exemplified descriptions do not constitute limitations on the embodiments. Elements with the same reference numerals in the drawings represent similar elements, and unless otherwise stated, the figures in the drawings do not constitute proportional limitations.

[0053] Figure 1 A schematic diagram of a bone density measurement method provided in an embodiment of the present application;

[0054] Figure 2 A schematic diagram of another bone density measurement method provided in an embodiment of the present application;

[0055] Figure 3 A schematic diagram of the system structure provided in the embodiment of the present application;

[0056] Figure 4 An image processing flow chart provided for an embodiment of the present application;

[0057] Figure 5 A scatter correction processing operation flow chart provided in an embodiment of the present application;

[0058] Figure 6 A schematic diagram of the structure of a bone density measurement device provided in an embodiment of the present application;

[0059] Figure 7 A schematic diagram of the structure of an electronic device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0060] Data show that by 2024, there will be about 100 million osteoporosis patients in my country. With the intensification of the aging process in my country, osteoporosis has become an important factor affecting the quality of life of the elderly. The measurement of bone density mainly relies on dedicated pencil beam or fan beam dual energy X-ray absorptiometry DEXA and digital X-ray photography system DR to measure bone density.

[0061] At present, most of the DEXA bone densitometers come from foreign manufacturers and are expensive. Among them, although the scattering of the pencil beam scanning method is negligible, the scanning speed is very slow. The fan beam scanning method adds a narrow slit collimator in front of the tube to obtain fan beam rays. This method shortens the scanning time compared to the pencil beam by increasing the single scanning area. However, this method reduces the utilization rate of the rays because the rays must pass through the narrow slit collimator first; and because of scattering, the accuracy of the bone density value decreases.

[0062] At present, there are two main measurement methods based on digital X-ray photography systems:

[0063] One method requires the use of a standard body for reference. A standard body with a known density is made of a material with a similar mineral density to that of human bones. During measurement, it is exposed and imaged under the same conditions as the part of the human body to be measured. The relative values ​​of the images of the human bone area and the standard body area are used to convert the pixel values ​​of the bone area into the bone density value of the standard body. This method requires the use of a standard body during image acquisition, which complicates the acquisition process and can only measure individual parts of the human body. The bone density of complex parts such as the lumbar spine cannot be accurately measured.

[0064] Another method requires the use of a dedicated scatter correction lead plate, through circular holes arranged in a matrix form. In the scanned image, since one area is completely blocked, while the X-rays in another area can pass through, the scattered light in the completely blocked area is used to estimate the scattered light in the unblocked area. This method requires switching the optical path to repeat the measurement to obtain a normal X-ray image without the lead plate and an X-ray image with the lead plate. Under dual-energy irradiation conditions, four images of the patient need to be obtained, which increases the complexity of scanning acquisition and the X-ray radiation dose received by the patient. It is difficult to truly promote it in clinical practice.

[0065] Therefore, in an embodiment of the present application, a bone density measurement method, device, equipment and storage medium are provided. This solution utilizes the rapid cone beam scanning of a digital X-ray photography system to achieve rapid and accurate bone density measurement by removing scattered components in the X-ray image.

[0066] In order to make the purpose, technical solution and advantages of the embodiments of the present application clearer, the technical solution in the embodiments of the present application will be clearly and completely described below in conjunction with the drawings in the embodiments of the present application. Obviously, the described embodiments are part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of this application.

[0067] The disclosure below provides many different embodiments or examples to implement different structures of the present invention. In order to simplify the disclosure of the present invention, the parts and settings of specific examples are described below. Of course, they are only examples, and the purpose is not to limit the present invention. In addition, the present invention can repeat reference numbers and / or letters in different examples. This repetition is for the purpose of simplification and clarity, and does not itself indicate the relationship between the various embodiments and / or settings discussed.

[0068] See also Figure 1 , is a flow chart of a bone density measurement method provided in an embodiment of the present application, the method specifically comprises the following steps:

[0069] S101, obtaining an original medical image; wherein the original medical image includes a high-energy original medical image and a low-energy original medical image;

[0070] In this application, when acquiring the original medical image, the original medical image can be acquired by ordinary data acquisition method, and no additional hardware such as bone density standard body and scatter correction lead plate is required. For example: the original medical image is acquired by an ordinary digital X-ray photography system. In addition, this application does not need to acquire four images of the patient, but only needs to continuously acquire two high-energy and low-energy images under the same environment, which simplifies the complexity of bone density measurement; this application refers to the image acquired under high-energy conditions as a high-energy original medical image, and the image acquired under low-energy conditions as a low-energy original medical image.

[0071] S102, performing an image processing operation on the original medical image to obtain a target medical image; the image processing operation includes a scatter correction processing operation, and the scatter correction processing operation removes the scatter component of the original medical image by simulating scatter distribution;

[0072] In the present application, after acquiring the original medical image, it is necessary to perform image processing operations on the original medical image. The image processing operations include scatter correction processing operations, which remove the scattering components of the original medical image by simulating scatter distribution, thereby avoiding affecting the accuracy of bone density measurement when measuring bone density.

[0073] In addition, the image processing operations in the present application may include other operations to improve the accuracy of bone density measurement, such as flat plate correction operations, noise reduction operations, etc., in addition to the scatter correction processing operations, so as to further improve the measurement accuracy of bone density through multiple processing operations.

[0074] When performing image processing operations, the present application needs to process the high-energy original medical image and the low-energy original medical image of the original medical graphics respectively to obtain corresponding target medical images, which target medical images include: high-energy target medical images and low-energy target medical images. That is: after performing various image processing operations on the high-energy original medical image, the high-energy target medical image is obtained, and after performing various image processing operations on the low-energy original medical image, the low-energy target medical image is obtained.

[0075] S103, determining a first attenuation image using the target medical image and the air image; wherein the air image includes a high-energy air image and a low-energy air image, and the first attenuation image includes a first high-energy attenuation image and a first low-energy attenuation image;

[0076] After obtaining the processed target medical image, the present application also needs to obtain an air image, which needs to be collected and fitted in advance. The air image refers to two sets of low-energy and high-energy air images obtained by aerial photography under a digital X-ray photography system. Therefore, the air image includes a high-energy air image and a low-energy air image. Similarly, the first attenuation image determined by the present application also includes: a first high-energy attenuation image and a first low-energy attenuation image.

[0077] That is, when determining the first attenuation image, the present application needs to use the high-energy target medical image and the high-energy air image to calculate the first high-energy attenuation image, and use the low-energy target medical image and the low-energy air image to calculate the first low-energy attenuation image.

[0078] When determining the first high-energy attenuation image and the first low-energy attenuation image, the present application can specifically determine them through an attenuation image calculation formula, for example: determining the first high-energy attenuation image through a high-energy attenuation calculation formula, and determining the first low-energy attenuation image through a low-energy attenuation calculation formula.

[0079] Among them, the high energy attenuation calculation formula is:

[0080] x1=ln(I 0H / I H1 )

[0081] The low energy attenuation calculation formula is:

[0082] y1=ln(I 0L / I L1 )

[0083] Among them, x1 is the first high energy attenuation image, I0H For high-energy air images, I H1 is a high-energy target medical image, y1 is the first low-energy attenuation image, I 0L is a low-energy air image, I L1 For low-energy target medical images.

[0084] S104: Determine a bone density value according to the first attenuation image and a bone density calculation rule.

[0085] In the present application, the bone density calculation rules can be determined in advance, and the bone density value can be measured through the first high-energy attenuation image and the first low-energy attenuation image in the first attenuation image and the bone density calculation rules. When determining the bone density calculation rules in the present application, it is first necessary to determine the polynomial coefficients in the bone density calculation rules through multiple experiments, for example: obtain the air image required for the experimental process, and the test image of each combination of aluminum plates and glass plates of each thickness, determine the attenuation image based on the air image and the test image, use the attenuation image as the independent variable, and use the bone density corresponding to the aluminum plates of different thicknesses as the dependent variable, perform a 5th-order polynomial fitting, obtain the polynomial coefficients, and then determine the final bone density calculation rules.

[0086] In summary, it can be seen that when measuring bone density, the present application does not need to use additional hardware such as bone density standards and scatter correction lead plates. It only needs to obtain high-energy original medical images and low-energy original medical images, and perform image processing operations including scatter correction processing operations on them, so as to effectively remove the scattering components and improve the speed and accuracy of bone density measurement.

[0087] See also Figure 2 , is a flow chart of another bone density measurement method provided in an embodiment of the present application, the method specifically comprises the following steps:

[0088] S201, acquiring an original medical image through a digital X-ray photography system; wherein the original medical image is an image generated after scattering processing through a grid filter, and the original medical image includes a high-energy original medical image and a low-energy original medical image;

[0089] S202, performing a flat panel correction processing operation, a bad channel correction processing operation, an overexposure correction processing operation, a scatter correction processing operation, and a noise reduction processing operation on the original medical image to obtain a target medical image; wherein the target medical image includes: a high-energy target medical image and a low-energy target medical image; the scatter correction processing operation removes the scattering component of the original medical image by simulating scatter distribution;

[0090] S203, segmenting a region of interest image in the target medical image; wherein the region of interest image includes: a high-energy region of interest image and a low-energy region of interest image;

[0091] S204, determining a first attenuation image using the region of interest image and the air image; wherein the air image includes a high-energy air image and a low-energy air image, and the first attenuation image includes a first high-energy attenuation image and a first low-energy attenuation image;

[0092] S205: Determine a bone density value according to the first attenuation image and a bone density calculation rule.

[0093] In the present application, a digital X-ray photography system is used to acquire original medical images. When acquiring original medical images through the digital X-ray photography system, no additional hardware such as bone density standards and scatter correction lead plates is required. It is only necessary to continuously acquire high-energy and low-energy images under the same environment, that is, to acquire high-energy original medical images and low-energy original medical images.

[0094] See also Figure 3 , is a schematic diagram of the system structure provided in an embodiment of the present application. The system includes a ray source A1, an irradiated object A3, a grid A4, and a flat-panel detector A5. The main irradiated light A2 and the scattered light A6 in the figure are the issues that need to be focused on in the system design. The grid is a component used to block and reduce scattered light in a digital X-ray photography system. Although the grid can greatly reduce the scattered light reaching the flat-panel detector, it cannot completely block the scattered light. Therefore, in the present application, the system needs to combine the software scatter correction method with the grid hardware to remove the scattered light, so as to achieve the maximum removal of the scattered components in the final X-ray image.

[0095] Therefore, after obtaining the original medical image, in order to achieve accurate bone density calculation, this application will perform strict image processing operations on the original medical image, see Figure 4 , is an image processing flow chart provided in an embodiment of the present application. It can be seen from the flow chart that the image processing operations performed by the present application on the original medical image include: flat plate correction processing operation B1, bad channel correction processing operation B2, overexposure correction processing operation B3, scatter correction processing operation B4 and noise reduction processing operation B5 to obtain the target medical image.

[0096] Among them, the flat panel correction processing operation B1 can reduce the non-uniformity of the response of the flat panel detector and the influence of the anode effect of the X-ray tube itself; the bad channel correction processing operation B2 can prevent the bad channel influence that may appear in the flat panel detector; the overexposure correction processing operation B3 can prevent the overexposure of the local area due to the uneven thickness of the irradiated object in the actual scanning; the scattering correction processing operation B4 is a software correction process based on the use of the filter grid to remove the scattering components in the X-ray image as much as possible. This part has the greatest impact on the accuracy of the final bone density measurement; the noise reduction processing operation B5 is after the scattering components are removed, because the quantum noise caused by various factors still exists in the image, it may affect the accuracy of the bone density measurement, so it is necessary to add the noise reduction processing step. The present application executes the above B1-B5 on the original medical image to obtain the target medical image, including: executing the above B1-B5 on the high-energy original medical image to obtain the high-energy target medical image, and executing the above B1-B5 on the low-energy original medical image to obtain the low-energy target medical image.

[0097] In the present application, after acquiring the target medical image, it is necessary to segment the region of interest image from the target medical image, and the region of interest image includes: a high-energy region of interest image in the high-energy target medical image, and a low-energy region of interest image in the low-energy target medical image; for example: the region of interest can be lumbar vertebrae L1-L4 (first lumbar vertebra-fourth lumbar vertebra). Then, based on the high-energy region of interest image and the high-energy air image, a first high-energy attenuation image is determined, and based on the low-energy region of interest image and the low-energy air image, a first low-energy attenuation image is determined, and finally, based on the first high-energy attenuation image, the first low-energy attenuation image and the bone density calculation rule, the bone density value is determined; when segmenting the region of interest image, the present application can be manually segmented by the user, or automatically segmented by a network model, which is not specifically limited here.

[0098] In summary, the present application can improve the accuracy of bone density calculation by performing flat panel correction processing operations, bad channel correction processing operations, overexposure correction processing operations, scatter correction processing operations and noise reduction processing operations on the original medical image; and the present application utilizes a conventional digital X-ray photography system DR to achieve fast and efficient bone density measurement, and removes scatter by combining filter grid hardware and scatter correction software to achieve high-precision bone density calculation.

[0099] See also Figure 5 , is a scatter correction processing operation flow chart provided in an embodiment of the present application, and the process specifically includes the following steps:

[0100] S301, determining a second attenuation image using the image to be processed and the air image, and using the second attenuation image as an initial image; wherein the image to be processed is an image that needs to perform a scatter correction processing operation;

[0101] In the present application, the image to be processed refers to the image output after the previous processing operation and needs to perform a scatter correction processing operation. If the previous processing operation is an overexposure correction processing operation, the image to be processed is the image output by the overexposure correction processing operation. The image to be processed includes: a high-energy image to be processed and a low-energy image to be processed. The air images in the present application include: a high-energy air image and a low-energy air image, and the second attenuation image includes: a second high-energy attenuation image and a second low-energy attenuation image. Among them, the second high-energy attenuation image is: generated using the high-energy attenuation calculation formula in the above-mentioned embodiment, as well as the high-energy image to be processed and the high-energy air image, and the second low-energy attenuation image is: generated using the low-energy attenuation calculation formula in the above-mentioned embodiment, as well as the low-energy image to be processed and the low-energy air image, that is:

[0102] The process of calculating the second high energy attenuation image by the high energy attenuation calculation formula is:

[0103] x2=ln(I 0H / I H2 )

[0104] The process of calculating the second low energy attenuation image by the low energy attenuation calculation formula is:

[0105] y2=ln(I 0L / I L2 )

[0106] Among them, x2 is the second high energy attenuation image, I 0H For high-energy air images, I H2 is the high-energy image to be processed, y2 is the second low-energy attenuation image, I 0L is a low-energy air image, I L2 It is a low-energy image to be processed.

[0107] S302, determining the equivalent water thickness of each pixel in the initial image;

[0108] In the present application, before determining the equivalent water thickness, it is also necessary to input the X-ray physical parameters corresponding to the device, which are the physical parameters used when calculating the equivalent water thickness, such as the size of the scattering kernel, etc. Therefore, if the initial image is the second attenuation image, and the second attenuation image includes the second high-energy attenuation image and the second low-energy attenuation image, it is necessary to determine the equivalent water thickness of each pixel in the second high-energy attenuation image and the equivalent water thickness of each pixel in the second low-energy attenuation image according to the physical parameters. If the initial image is the main light image of S308, and the main light image includes the high-energy main light image and the low-energy main light image, it is necessary to calculate the equivalent water thickness of each pixel in the high-energy main light image and the equivalent water thickness of each pixel in the low-energy main light image according to the physical parameters.

[0109] S303, determining the scattering core of each pixel point according to the equivalent water thickness of each pixel point;

[0110] In this application, in order to determine the corresponding scattering kernel by the equivalent water thickness of each pixel, it is necessary to pre-simulate the scattering kernel corresponding to different water thicknesses. In order to realize software scattering correction, this application uses Monte Carlo simulation software to model and obtain the scattering kernel. The process includes the following steps: obtaining two sets of low-energy and high-energy energy spectra of the device, and importing them into Monte Carlo software, constructing a phantom (water), a filter grid, a detector (such as cesium iodide), etc. in the Monte Carlo software; based on the above Monte Carlo model, simulating a pencil beam with an energy spectrum, shining it on water of different thicknesses, and obtaining the scattering distribution, that is, the scattering kernel. Through the above process, the corresponding relationship between different water thicknesses and the scattering kernel can be obtained.

[0111] Therefore, after obtaining the equivalent water thickness of each pixel in the initial image, the present application can determine the scattering kernel corresponding to the equivalent water thickness of each pixel according to the above correspondence. The scattering kernel is saved in the form of a data file, each data file corresponds to a water thickness, and each water thickness will simulate a scattering kernel.

[0112] S304, superimposing the scattering kernel of each pixel point with the initial image to obtain a first scattering distribution image; wherein the scattering distribution image of the current cycle is the first scattering distribution image, and the scattering distribution image of the previous cycle is the second scattering distribution image;

[0113] In the present application, after determining the scattering kernel of each pixel point in the initial image, each scattering kernel needs to be superimposed with the initial image, and the superposition method can be a convolution operation or other forms, which are not specifically limited here. After superimposing the scattering kernel of each pixel point with the initial image, the present application generates a first scattering distribution image, and the first scattering distribution image includes: a first high-energy scattering distribution image and a first low-energy scattering distribution image.

[0114] S305, determining whether there is a second scattering distribution image in the previous cycle;

[0115] If yes, execute S306; if no, execute S308;

[0116] In order to clearly describe each cycle, the present application refers to the scattering distribution image generated in the current cycle as the first scattering distribution image, and the scattering distribution image generated in the previous cycle as the second scattering distribution image. Therefore, the second scattering distribution image includes: a second high-energy scattering distribution image and a second low-energy scattering distribution image. If the current cycle is the first cycle, there is no second scattering distribution image. Therefore, in S305, if it is determined that there is a second scattering distribution image of the previous cycle, it means that the current cycle is not the first cycle, and S306 is executed. Otherwise, it means that the current cycle is the first cycle, and S308 is continued to be executed to continue to execute the next cycle.

[0117] S306, calculating the difference between the first scattering distribution image and the second scattering distribution image;

[0118] S307, determining whether the difference is less than a predetermined threshold;

[0119] If not, execute S308; if yes, execute S309;

[0120] When calculating the difference between the first scattering distribution image and the second scattering distribution image, the present application may calculate the first difference between the first high-energy scattering distribution image and the second high-energy scattering distribution image, calculate the second difference between the first low-energy scattering distribution image and the second low-energy scattering distribution image, and determine the magnitude relationship between the first difference and the second difference and the predetermined threshold.

[0121] When calculating the difference between the first scatter distribution image and the second scatter distribution image, the present application specifically calculates the difference between the pixel values ​​of corresponding pixels in the two images, and takes the sum of the differences of the pixels as the difference between the two images.

[0122] S308, calculating a main light image according to the second attenuation image and the first scattering distribution image, and taking the main light image as the initial image, and continuing to execute S302;

[0123] When the present application calculates the main light image according to the second attenuation image and the first scattering distribution image, if the first difference between the first high-energy scattering distribution image and the second high-energy scattering distribution image is not less than a predetermined threshold, the high-energy main light image is calculated according to the second high-energy attenuation image and the first high-energy scattering distribution image; if the second difference between the first low-energy scattering distribution image and the second low-energy scattering distribution image is not less than the predetermined threshold, the low-energy main light image is calculated according to the second low-energy attenuation image and the first low-energy scattering distribution image. After the high-energy main light image and / or the low-energy main light image are calculated, the high-energy main light image and / or the low-energy main light image are used as the initial image, and S302 is continued to be executed to start the next cycle process.

[0124] S309: Calculate a main light image according to the second attenuation image and the first scattering distribution image, and use the main light image as a scattering correction processing result.

[0125] In the present application, if the first difference is less than a predetermined threshold, a high-energy main light image is calculated based on the second high-energy attenuation image and the first high-energy scattering distribution image, and used as a scattering correction processing result; if the second difference is not less than a predetermined threshold, a low-energy main light image is calculated based on the second low-energy attenuation image and the first low-energy scattering distribution image, and used as a scattering correction processing result. In other words, the present application performs a scattering correction processing operation on the high-energy image to be processed, and performs a scattering correction processing operation on the low-energy image to be processed. These are two independent operations, and the scattering correction processing results finally obtained are the scattering correction processing results of the high-energy image to be processed and the scattering correction processing results of the low-energy image to be processed. The present application can obtain a main light image by calculating the difference between the second attenuation image and the first scattering distribution image.

[0126] Furthermore, in order to improve the speed and execution efficiency of image processing, the present application may, when the second attenuation image is used as the initial image in S301, downsample the second attenuation image to obtain a downsampled image, and use the downsampled image as the initial image; correspondingly, when the scattering kernel of each pixel point is superimposed with the initial image in S304 to obtain a first scattering distribution image, the scattering kernel of each pixel point may be superimposed with the initial image to obtain a superimposed image, and the superimposed image may be upsampled to obtain the first scattering distribution image; correspondingly, when the main light image is used as the initial image, it includes: downsampling the main light image to obtain a downsampled main light image, and using the downsampled main light image as the initial image.

[0127] Among them, if the second attenuation image is a second high-energy attenuation image, the second high-energy attenuation image is downsampled to obtain a high-energy downsampled image, and the high-energy downsampled image is used as the initial image to continue to execute S302; if the second attenuation image is a second low-energy attenuation image, the second low-energy attenuation image is downsampled to obtain a low-energy downsampled image, and the low-energy downsampled image is used as the initial image to continue to execute S302; correspondingly, after the scattering kernel of each pixel point of the high-energy downsampled image is superimposed with the high-energy downsampled image to obtain a high-energy superposition image, it is necessary to upsample the high-energy superposition image to obtain a first high-energy scattering distribution image; after the scattering kernel of each pixel point of the low-energy downsampled image is superimposed with the low-energy downsampled image to obtain a low-energy superposition image, it is necessary to upsample the low-energy superposition image to obtain a first low-energy scattering distribution image. Moreover, when S308 uses the high-energy main light image as the initial image, it is also necessary to downsample the high-energy main light image to obtain the high-energy downsampled main light image, and use the high-energy downsampled main light image as the initial image to continue executing S302; when S308 uses the low-energy main light image as the initial image, it is also necessary to downsample the low-energy main light image to obtain the low-energy downsampled main light image, and use the low-energy downsampled main light image as the initial image to continue executing S302.

[0128] In summary, it can be seen that the present application can determine the first scattering distribution image of the second attenuation image by determining the equivalent water thickness of each pixel point in the second attenuation image, and then perform scattering correction on the second attenuation image according to the first scattering distribution image to achieve effective removal of scattering; and, the present application can also improve the speed and execution efficiency of image processing by downsampling the image, thereby improving the measurement speed of bone density.

[0129] In another embodiment provided in the present application, after acquiring the original medical image, a process of acquiring an air image is also included, and the process includes: determining the actual mAs value of the original medical image; obtaining the air image by fitting the pre-collected initial air image; the mAs value of the air image is the same as the actual mAs value.

[0130] In the present application, in order to calculate the low-energy attenuation image and the high-energy attenuation image, it is necessary to pre-collect and fit the air image. Under the digital X-ray photography system, two groups of high-energy air images and low-energy air images are obtained respectively. Since the image will be overexposed when mAs (milliampere-seconds, used to indicate the exposure of X-rays) is too large, several groups of relatively small mAs values ​​are used to collect air images in the present application. After the original medical image is collected, the actual mAs of the original medical image is first determined, and the high-energy air image with a relatively small mAs is fitted to obtain a high-energy original medical image with the same mAs value as the actual collection. The low-energy air image with a relatively small mAs is fitted to obtain a low-energy original medical image with the same mAs value as the actual collection. When fitting the image in the present application, a linear fitting method can be used for processing.

[0131] It can be seen that the present application, by pre-collecting air images with smaller mAs values, can obtain air images with the same actual mAs values ​​through fitting when processing original medical images, thereby avoiding overexposure of air images and improving the accuracy of bone density calculation; and this air image fitting method can provide a stable bone density measurement solution for clinical applications.

[0132] In another embodiment provided by the present application, the process of determining the bone density value according to the first attenuation image and the bone density calculation rule specifically includes:

[0133] Inputting the first attenuation image into a bone density calculation rule to determine a bone density value;

[0134] The bone density calculation rules are:

[0135] bmd(x,y)=p00+p10*x+p01*y+p20*x 2 +p11*x*y+

[0136] p02*y 2 +p21*x 2 *y+p12*x*y 2 +p03*y 3 +p22*x 2 *y 2 +p13*

[0137] x*y 3 +p04*y 4 +p23*x 2 *y 3 +p14*x*y 4 +p05*y 5 ;

[0138] Among them, bmd is the bone density value, x is the first high-energy attenuation image, y is the first low-energy attenuation image, p00 is the first coefficient, p10 is the second coefficient, p01 is the third coefficient, p20 is the fourth coefficient, p11 is the fifth coefficient, p02 is the sixth coefficient, p21 is the seventh coefficient, p12 is the eighth coefficient, p03 is the ninth coefficient, p22 is the tenth coefficient, p13 is the eleventh coefficient, p04 is the twelfth coefficient, p23 is the thirteenth coefficient, p14 is the fourteenth coefficient, and p05 is the fifteenth coefficient.

[0139] In this application, it is first necessary to determine the polynomial coefficients in the bone density calculation rule through multiple experiments. The process includes:

[0140] Take aerial photos under a digital X-ray photography system to obtain high-energy air images and low-energy air images respectively; use different combinations of 1-15 mm aluminum plates and 1-25 cm PMMA (acrylic) glass plates to conduct experiments, and obtain high-energy experimental images and low-energy experimental images respectively under a digital X-ray photography system. Then, based on the high-energy attenuation calculation formula and low-energy attenuation calculation formula in the above embodiment, calculate high-energy experimental attenuation images and low-energy experimental attenuation images of different combinations. That is:

[0141] The process of calculating the high energy experimental attenuation image by the high energy attenuation calculation formula is:

[0142] x3=ln(I 0H / I H3 )

[0143] The process of calculating the low-energy experimental attenuation image by the low-energy attenuation calculation formula is:

[0144] y3=ln(I 0L / I L3 )

[0145] Among them, x3 is the high energy experimental attenuation image, I 0H For high-energy air images, I H3 is the high energy experimental image, y3 is the low energy experimental attenuation image, I 0L is a low-energy air image, I L3 This is a low-energy experimental image.

[0146] Taking the high-energy attenuation images and low-energy attenuation images corresponding to the above-mentioned different combinations as independent variables, and the bone density corresponding to the aluminum plates of different thicknesses as the dependent variable, a 5th-order polynomial fitting is performed to obtain the polynomial coefficients, which are the first to fifteenth coefficients in the bone density calculation formula. After substituting the above-mentioned polynomial coefficients into the bone density calculation rules, the final bone density calculation rules can be determined. Therefore, after obtaining the first attenuation image, the present application can input the first attenuation image into the bone density calculation rules to determine the bone density value.

[0147] In summary, the present application utilizes a conventional digital X-ray photography system to provide an alternative to the dedicated dual-energy X-ray bone densitometer DEXA. This solution does not require the use of any standard body for reference, does not require the use of additional scatter correction lead plates, increases the adaptability of bone density measurement sites, supports bone density measurement in complex sites such as the lumbar spine, reduces unnecessary repeated measurements and the resulting increase in radiation dose, improves measurement speed and efficiency, and makes large-scale clinical promotion and application possible.

[0148] See also Figure 6 , Figure 6 A schematic diagram of the structure of a bone density measurement device provided in an embodiment of the present application, the device specifically comprises:

[0149] The acquisition module 11 is used to acquire original medical images; wherein the original medical images include high-energy original medical images and low-energy original medical images;

[0150] A processing module 12 is used to perform an image processing operation on the original medical image to obtain a target medical image; the image processing operation includes a scatter correction processing operation, and the scatter correction processing operation removes the scatter component of the original medical image by simulating scatter distribution;

[0151] A first determination module 13 is used to determine a first attenuation image using the target medical image and the air image; wherein the air image includes a high-energy air image and a low-energy air image, and the first attenuation image includes a first high-energy attenuation image and a first low-energy attenuation image;

[0152] The second determination module 14 is used to determine the bone density value according to the first attenuation image and the bone density calculation rule.

[0153] As an optional embodiment, the processing module includes a scatter correction processing unit, and the scatter correction processing unit includes:

[0154] An attenuation image determination subunit, used to determine a second attenuation image using the image to be processed and the air image;

[0155] A first initial image determination subunit is used to use the second attenuation image as an initial image; wherein the image to be processed is an image that needs to perform a scatter correction processing operation;

[0156] A water thickness determination subunit, used to determine the equivalent water thickness of each pixel in the initial image;

[0157] A scattering core determination subunit, used to determine the scattering core of each pixel point according to the equivalent water thickness of each pixel point;

[0158] A superposition subunit is used to superimpose the scattering kernel of each pixel point with the initial image to obtain a first scattering distribution image; wherein the scattering distribution image of the current cycle is the first scattering distribution image, and the scattering distribution image of the previous cycle is the second scattering distribution image;

[0159] A first calculation subunit is used to calculate a main light image according to the second attenuation image and the first scattering distribution image when the difference between the first scattering distribution image and the second scattering distribution image is less than a predetermined threshold, and use the main light image as a scattering correction processing result;

[0160] A second calculation subunit is configured to calculate a main light image according to the second attenuation image and the first scattering distribution image if there is no second scattering distribution image or if the difference between the first scattering distribution image and the second scattering distribution image is not less than a predetermined threshold;

[0161] The second initial image determination subunit is used to take the main light image as the initial image and trigger the water thickness determination subunit.

[0162] As an optional embodiment, the first initial image determination subunit is specifically used to: perform downsampling processing on the second attenuated image to obtain a downsampled image, and use the downsampled image as the initial image;

[0163] The superposition subunit is specifically used for: superimposing the scattering kernel of each pixel point with the initial image to obtain a superimposed image, and performing upsampling processing on the superimposed image to obtain a first scattering distribution image.

[0164] The second initial image determination subunit is specifically used for: performing downsampling processing on the main light image to obtain a downsampled main light image, and using the downsampled main light image as the initial image.

[0165] As an optional embodiment, the acquisition module is specifically used to: acquire an original medical image through a digital X-ray photography system; wherein the original medical image is an image generated after scattering processing is performed through a grid filter.

[0166] As an optional embodiment, the processing module is specifically used to: perform a flat panel correction processing operation, a bad channel correction processing operation, an overexposure correction processing operation, a scatter correction processing operation and a noise reduction processing operation on the original medical image to obtain a target medical image; wherein the target medical image includes: a high-energy target medical image and a low-energy target medical image.

[0167] As an optional embodiment, the first determining module includes:

[0168] A segmentation unit, used for segmenting a region of interest image in the target medical image; wherein the region of interest image includes: a high-energy region of interest image and a low-energy region of interest image;

[0169] A determining unit is used to determine a first attenuation image using the region of interest image and the air image.

[0170] As an optional embodiment, the bone density measuring device further includes:

[0171] A third determination module, configured to determine an actual mAs value of the original medical image;

[0172] A fitting module is used to obtain an air image by fitting a pre-collected initial air image; the mAs value of the air image is the same as the actual mAs value.

[0173] As an optional embodiment, the second determination module is specifically used to: input the first attenuation image into a bone density calculation rule to determine a bone density value;

[0174] The bone density calculation rule is:

[0175] bmd(x,y)=p00+p10*x+p01*y+p20*x 2 +p11*x*y+

[0176] p02*y 2 +p21*x 2 *y+p12*x*y 2 +p03*y 3 +p22*x 2 *y 2 +p13*x*y 3 +p04*y 4 +p23*x 2 *y 3 +p14*x*y 4 +p05*y 5 ;

[0177] Among them, bmd is the bone density value, x is the first high-energy attenuation image, y is the first low-energy attenuation image, p00 is the first coefficient, p10 is the second coefficient, p01 is the third coefficient, p20 is the fourth coefficient, p11 is the fifth coefficient, p02 is the sixth coefficient, p21 is the seventh coefficient, p12 is the eighth coefficient, p03 is the ninth coefficient, p22 is the tenth coefficient, p13 is the eleventh coefficient, p04 is the twelfth coefficient, p23 is the thirteenth coefficient, p14 is the fourteenth coefficient, and p05 is the fifteenth coefficient.

[0178] Regarding the device in the above embodiment, the specific manner in which each module performs operations has been described in detail in the embodiment of the method, and will not be elaborated here.

[0179] See also Figure 7 , Figure 7 A schematic diagram of the structure of an electronic device provided in an embodiment of the present application, the electronic device specifically includes:

[0180] A processor 21, a memory 22, and a computer program stored in the memory 22 and executable on the processor 21. The processor 21 executes the steps of the bone density measurement method described in any of the above method embodiments through the computer program.

[0181] Among them, the processor 21 may include one or more processing cores, such as a 4-core processor, an 8-core processor, etc. The processor 21 can be implemented in at least one hardware form of DSP (Digital Signal Processing), FPGA (Field-Programmable Gate Array), and PLA (Programmable Logic Array). The processor 21 may also include a main processor and a coprocessor. The main processor is a processor for processing data in the awake state, also known as a CPU (Central Processing Unit); the coprocessor is a low-power processor for processing data in the standby state. In some embodiments, the processor 21 may be integrated with a GPU (Graphics Processing Unit), which is responsible for rendering and drawing the content to be displayed on the display screen. In some embodiments, the processor 21 may also include an AI (Artificial Intelligence) processor, which is used to process computing operations related to machine learning.

[0182] The memory 22 may include one or more computer-readable storage media, which may be non-transitory. The memory 22 may also include a high-speed random access memory, and a non-volatile memory, such as one or more disk storage devices, flash memory storage devices. In this embodiment, the memory 22 is at least used to store the following computer program 221, wherein, after the computer program is loaded and executed by the processor 21, it can implement the relevant steps in the bone density measurement method disclosed in any of the aforementioned embodiments. In addition, the resources stored in the memory 22 may also include an operating system 222 and data 223, etc., and the storage method may be temporary storage or permanent storage. Among them, the operating system 222 may include Windows, Unix, Linux, etc.

[0183] In some embodiments, the electronic device may further include a display screen 23 , an input / output interface 24 , a communication interface 25 , a sensor 26 , a power source 27 , and a communication bus 28 .

[0184] certainly, Figure 7 The structure of the electronic device shown does not constitute a limitation on the electronic device in the embodiments of the present application. In actual applications, the electronic device may include Figure 7 More or fewer components than shown, or combinations of certain components.

[0185] In another exemplary embodiment, a computer storage medium is also provided, and when the program instructions are executed by a processor, the steps of the bone density measurement method described in any of the above method embodiments are implemented. The storage medium may include: a USB flash drive, a mobile hard disk, a read-only memory (ROM), a random access memory (RAM), a magnetic disk or an optical disk, and other media that can store program codes.

[0186] Optionally, the specific examples in this embodiment may refer to the examples described in the above embodiments, and this embodiment will not be described in detail here.

[0187] It should be understood that the terms used herein are only for the purpose of describing specific example embodiments and are not intended to be limiting. Unless the context clearly indicates otherwise, the singular forms "one", "an" and "said" as used herein may also be meant to include plural forms. The terms "include", "comprise", "contain", and "have" are inclusive, and therefore specify the existence of stated features, steps, operations, elements and / or parts, but do not exclude the existence or addition of one or more other features, steps, operations, elements, parts, and / or combinations thereof. The method steps, processes, and operations described herein are not interpreted as necessarily requiring them to be performed in the specific order described or illustrated, unless the execution order is clearly indicated. It should also be understood that additional or alternative steps may be used.

[0188] The foregoing is merely a specific embodiment of the present invention, which enables those skilled in the art to understand or implement the present invention. Various modifications to these embodiments will be apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the present invention. Therefore, the present invention will not be limited to the embodiments shown herein, but rather to the widest scope consistent with the principles and novel features claimed herein.

Claims

1. A method for measuring bone density, characterized in that: include: Acquire an original medical image; wherein the original medical image includes a high-energy original medical image and a low-energy original medical image; Performing an image processing operation on the original medical image to obtain a target medical image; the image processing operation includes a scatter correction processing operation, wherein the scatter correction processing operation removes the scatter component of the original medical image by simulating scatter distribution; Determine a first attenuation image using the target medical image and the air image; wherein the air image includes a high-energy air image and a low-energy air image, and the first attenuation image includes a first high-energy attenuation image and a first low-energy attenuation image; A bone density value is determined according to the first attenuation image and a bone density calculation rule.

2. The bone density measurement method according to claim 1, characterized in that: The scatter correction processing operation includes: Determine a second attenuation image using the image to be processed and the air image, and use the second attenuation image as the initial image; wherein the image to be processed is an image that needs to perform a scatter correction processing operation; Determine the equivalent water thickness of each pixel in the initial image; Determine the scattering kernel of each pixel point according to the equivalent water thickness of each pixel point; Superimposing the scattering kernel of each pixel point with the initial image to obtain a first scattering distribution image; wherein the scattering distribution image of the current cycle is the first scattering distribution image, and the scattering distribution image of the previous cycle is the second scattering distribution image; If the difference between the first scattering distribution image and the second scattering distribution image is less than a predetermined threshold, a main light image is calculated according to the second attenuation image and the first scattering distribution image, and the main light image is used as a scattering correction processing result; If the second scattering distribution image does not exist, or the difference between the first scattering distribution image and the second scattering distribution image is not less than a predetermined threshold, the main light image is calculated according to the second attenuation image and the first scattering distribution image, and the main light image is used as the initial image, and the step of determining the equivalent water thickness of each pixel in the initial image is continued.

3. The bone density measurement method according to claim 2, characterized in that: Using the second attenuated image as the initial image comprises: performing downsampling processing on the second attenuated image to obtain a downsampled image; Using the downsampled image as an initial image; Correspondingly, superimposing the scattering kernel of each pixel point with the initial image to obtain the first scattering distribution image includes: The scattering kernel of each pixel point is superimposed with the initial image to obtain a superimposed image; performing upsampling processing on the superimposed image to obtain a first scattering distribution image; Accordingly, the main light image is used as the initial image, including: The main light image is downsampled to obtain a downsampled main light image, and the downsampled main light image is used as the initial image.

4. The bone density measurement method according to claim 1, characterized in that: The obtaining of the original medical image comprises: An original medical image is acquired through a digital X-ray photography system; wherein the original medical image is an image generated after scattering processing is performed through a grid filter.

5. The bone density measurement method according to claim 1, characterized in that: The performing of an image processing operation on the original medical image to obtain a target medical image includes: A flat panel correction processing operation, a bad channel correction processing operation, an overexposure correction processing operation, a scatter correction processing operation and a noise reduction processing operation are performed on the original medical image to obtain a target medical image; wherein the target medical image includes: a high-energy target medical image and a low-energy target medical image.

6. The bone density measurement method according to claim 1, characterized in that: Determining a first attenuation image using the target medical image and the air image includes: Segmenting the region of interest image in the target medical image; wherein the region of interest image includes: a high-energy region of interest image and a low-energy region of interest image; A first attenuation image is determined using the region of interest image and the air image.

7. The bone density measurement method according to claim 1, characterized in that: After obtaining the original medical image, the method further includes: Determining an actual mAs value of the original medical image; The air image is obtained by fitting the pre-collected initial air image; the mAs value of the air image is the same as the actual mAs value.

8. The bone density measurement method according to any one of claims 1 to 7, characterized in that: Determining the bone density value according to the first attenuation image and the bone density calculation rule includes: Inputting the first attenuation image into a bone density calculation rule to determine a bone density value; The bone density calculation rule is: bmd(x,y)=p00+p10*x+p01*y+p20*x 2 +p11*x*y+ p02*y 2 +p21*x 2 *y+p12*x*y 2 +p03*y 3 +p22*x 2 *y 2 +p13*x*y 3 +p04*y 4 +p23*x 2 *y 3 +p14*x*y 4 +p05*y 5 ; Among them, bmd is the bone density value, x is the first high-energy attenuation image, y is the first low-energy attenuation image, p00 is the first coefficient, p10 is the second coefficient, p01 is the third coefficient, p20 is the fourth coefficient, p11 is the fifth coefficient, p02 is the sixth coefficient, p21 is the seventh coefficient, p12 is the eighth coefficient, p03 is the ninth coefficient, p22 is the tenth coefficient, p13 is the eleventh coefficient, p04 is the twelfth coefficient, p23 is the thirteenth coefficient, p14 is the fourteenth coefficient, and p05 is the fifteenth coefficient.

9. A bone density measuring device, characterized in that: include: An acquisition module, used for acquiring original medical images; wherein the original medical images include high-energy original medical images and low-energy original medical images; A processing module, configured to perform an image processing operation on the original medical image to obtain a target medical image; the image processing operation includes a scatter correction processing operation, wherein the scatter correction processing operation removes the scatter component of the original medical image by simulating scatter distribution; A first determination module, configured to determine a first attenuation image using the target medical image and the air image; wherein the air image includes a high-energy air image and a low-energy air image, and the first attenuation image includes a first high-energy attenuation image and a first low-energy attenuation image; The second determination module is used to determine the bone density value according to the first attenuation image and the bone density calculation rule.

10. An electronic device, characterized in that: include: A processor, a memory, and a computer program stored in the memory and executable on the processor, wherein the processor executes the steps of the bone density measurement method described in any one of claims 1 to 8 of the present application through the computer program.

11. A computer storage medium, characterized in that: The computer storage medium stores computer executable instructions, and the computer executable instructions are used to execute the steps of the bone density measurement method described in any one of claims 1 to 8 of the present application.

Images