A flat panel detector and its image correction method

Abstract

This application provides a flat panel detector and its image correction method, including a flat panel detection module and an image correction module. The flat panel detection module includes a pixel array composed of pixel units and pseudo-pixel units, and the response sensitivity of the pseudo-pixel units is lower than that of the pixel units. Under the same exposure dose, the pseudo-pixel units generate smaller electrical signals than the pixel units. By utilizing the grayscale value fed back by the electrical signal of the pseudo-pixel units, and the quantitative relationship between grayscale and exposure dose, the true exposure dose of X-rays under oversaturated exposure dose can be calculated. Furthermore, the theoretical true grayscale value of the pixel unit under the true exposure dose of X-rays in the same area can be calculated, thereby improving the accuracy of image correction for the flat panel detector.

Description

Technical Field

[0001] This application relates to the field of digital medical imaging technology, and in particular to a flat panel detector and its image correction method. Background Technology

[0002] In digital radiography (DR), X-ray energy is converted into electrical signals by a flat panel detector. The flat panel detector can capture X-rays and convert the X-ray image of the object under test into a digital image for viewing, analysis, storage and dissemination. It is widely used in medical, biological, materials and industrial inspection fields.

[0003] In practical use, flat panel detectors, due to the non-uniformity of X-ray irradiation and the circuit characteristics and physical properties of semiconductor devices, can cause significant image retention and crosstalk caused by localized high-dose X-rays, manifesting as artifacts in the image. To address this phenomenon, image correction is often necessary, such as through improvements in device design and manufacturing processes, or by obtaining effective correction parameters through theoretical calculations and image patterns. However, when the X-ray exposure dose in a local area is oversaturated, the corresponding grayscale value remains constant and no longer increases with further exposure dose. This makes it impossible to obtain the theoretically true grayscale value of the oversaturated area, resulting in inaccurate image correction parameters and affecting the accuracy of image artifact correction.

[0004] Therefore, how to provide a flat panel detector and its image correction method that can quantitatively detect image grayscale under high doses of X-rays and improve the accuracy of flat panel detector image correction has become an urgent problem to be solved in this field. Summary of the Invention

[0005] The purpose of this application is to provide a flat panel detector and its image correction method, which can quantitatively detect the grayscale of images under high-dose X-rays and improve the accuracy of flat panel detector image correction.

[0006] In a first aspect, this application provides a flat panel detector, which includes:

[0007] The flat panel detection module is used to convert X-rays into electrical signals to generate X-ray images.

[0008] An image correction module, connected to the flat panel detection module, is used to receive the original image parameters of the X-ray image and output the corrected image parameters of the X-ray image.

[0009] The flat panel detection module includes a pixel array composed of pixel units and pseudo-pixel units, wherein the response sensitivity of the pseudo-pixel units is lower than that of the pixel units.

[0010] In one possible implementation, the pseudo-pixel units are uniformly arranged in the pixel array.

[0011] In one possible implementation, the image correction module includes a first correction unit and a second correction unit, wherein the first correction unit is used to correct crosstalk regions in the X-ray image; and the second correction unit is used to correct ghosting regions in the X-ray image.

[0012] In one possible implementation, the image correction module further includes a data management unit, which receives and stores the original image parameters of the X-ray image. The first correction unit and the second correction unit obtain the original image parameters from the data management unit and use different algorithms to correct the X-ray image, outputting the corrected image parameters of the X-ray image.

[0013] On the other hand, this application provides a flat panel detector image correction method, employing the flat panel detector described in any of the above embodiments, including:

[0014] The flat panel detector is placed directly facing the X-ray source, and the X-ray image is acquired using the flat panel detector module.

[0015] The image correction module receives the original image parameters of the X-ray image, performs crosstalk correction and ghosting correction on the X-ray image, and outputs the corrected image parameters.

[0016] In one possible implementation, the step of performing crosstalk correction on the X-ray image using the first correction unit specifically includes:

[0017] S11, Obtain the raw image parameters of the X-ray image through the data management unit;

[0018] S12, marking the first region and the crosstalk region in the X-ray image;

[0019] S13, calculate the grayscale correction value of each pixel unit in the crosstalk region using the grayscale value of each pixel unit in the first region;

[0020] Wherein, the first region is the region where the gray value of the pixel unit exceeds a first threshold, and the crosstalk region is the region where the gray value of the pixel unit is affected by the first region.

[0021] In one possible implementation, the step of using the second correction unit to correct for image retention in the X-ray image specifically includes:

[0022] S21, the raw image parameters of each frame of X-ray image are obtained through the data management unit;

[0023] S22, mark the first region in the X-ray image, and mark the afterimage region in the subsequent M frames of X-ray images;

[0024] S23, calculate the grayscale correction value of each pixel unit in the afterimage area using the grayscale value of each pixel unit in the first area;

[0025] Wherein, the first region is the region where the gray value of the pixel unit exceeds the first threshold, and the afterimage region is the region where the pixel unit in the first region affects the gray value of the pixel unit at the same position in the subsequent M frames of X-ray images.

[0026] In one possible implementation, the first region includes an unsaturated dose region and / or an oversaturated dose region, wherein the oversaturated dose region is the region where the pixel unit reaches a grayscale saturation value, and the unsaturated dose region is the region where the grayscale value of the pixel unit is between a first threshold and the grayscale saturation value.

[0027] In one possible implementation, the grayscale value of a pixel unit within the oversaturated region is calculated using the grayscale value of a pseudo-pixel unit within the oversaturated region.

[0028] In one possible implementation, the corrected image parameters include the grayscale correction value of each pixel unit in the crosstalk region and the grayscale correction value of each pixel unit in the afterimage region.

[0029] Compared with the prior art, the beneficial effects of this application are at least as follows:

[0030] This application provides a flat panel detector and its image correction method, including a flat panel detection module and an image correction module. The flat panel detection module includes a pixel array composed of pixel units and pseudo-pixel units, and the response sensitivity of the pseudo-pixel units is lower than that of the pixel units. Under the same exposure dose, the pseudo-pixel units generate smaller electrical signals than the pixel units. By utilizing the grayscale value fed back by the electrical signal of the pseudo-pixel units, and the quantitative relationship between grayscale and exposure dose, the true exposure dose of X-rays under oversaturated exposure dose can be calculated. Furthermore, the theoretical true grayscale value of the pixel unit under the true exposure dose of X-rays in the same area can be calculated, thereby improving the accuracy of image correction for the flat panel detector. Attached Figure Description

[0031] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of this application and should not be regarded as a limitation of the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.

[0032] Figure 1 This is a schematic diagram of a flat panel detector structure according to an embodiment of this application.

[0033] Figure 2 This is a schematic diagram of a pixel array structure according to an embodiment of this application.

[0034] Figure 3 This is a schematic diagram illustrating the positional relationship between a first region and a crosstalk region according to an embodiment of this application.

[0035] Figure 4 This is a schematic diagram illustrating the positional relationship between a first region and a residual region according to an embodiment of this application.

[0036] Illustration:

[0037] 100 Flat panel detection module; 110 Pixel array; 111 Pixel unit; 112 Pseudo-pixel unit; 200 Image correction module; 210 First correction unit; 220 Second correction unit; 230 Data management unit; 310 First region; 320 Crosstalk region; 321 Horizontal crosstalk region; 322 Vertical crosstalk region; 330 Ghosting region. Detailed Implementation

[0038] The following specific embodiments illustrate the implementation of this application. Those skilled in the art can easily understand other advantages and effects of this application from the content disclosed in this specification. This application can also be implemented or operated through other different specific embodiments, and various details in this application can also be modified or changed based on different viewpoints and applications without departing from the spirit of this application.

[0039] In the description of this application, it should be noted that, unless otherwise expressly specified and limited, the term "connection" should be interpreted broadly. For example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection or an indirect connection through an intermediate medium; it can be a connection within two components. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances. Furthermore, the terms "first" and "second," etc., are used only for distinguishing descriptions and should not be construed as indicating or implying relative importance.

[0040] The core component of the existing flat panel detector is the pixel array 110 with image sensing function in the flat panel detector module. When it senses incident X-rays, it converts the X-rays into electrical signals and outputs them to generate an X-ray image. The pixel unit will generate different electrical signals when it senses different doses of X-rays.

[0041] However, in practical applications, due to the non-uniformity of X-ray irradiation and the circuit characteristics of sensors and the physical properties of semiconductor devices, localized high-dose X-rays can cause significant afterimages and crosstalk, manifesting as artifacts in the image. To address this phenomenon, it is often necessary to correct the image output from the flat panel detector. This involves obtaining a quantitative relationship based on the specific X-ray exposure dose and spatial distribution, through theoretical calculations and image patterns, to acquire effective corrected image parameters. However, when the X-ray exposure dose in a local area exceeds the saturation dose that pixel unit 111 can feedback, the grayscale value of the pixel unit will remain constant and will no longer increase with the increase in exposure dose. Therefore, it is impossible to obtain the theoretical true grayscale value and exposure dose of the pixel unit under oversaturation conditions, resulting in inaccurate acquisition of image correction parameters and affecting the accuracy of image correction.

[0042] To address the aforementioned issues, the applicant discovered that by replacing some pixel units 111 in the pixel array of an existing flat panel detector with correspondingly lower-sensitivity pseudo-pixel units, it becomes possible to calculate the actual X-ray exposure dose and the theoretical true grayscale value of the pixel units in the same area when the X-ray exposure dose is oversaturated in a localized region. This allows for the calculation of more accurate image correction parameters for image artifacts. Based on this discovery, this application provides a flat panel detector and its image correction method to solve the problem of image correction failure caused by pixel units failing to report the theoretical true grayscale value and the actual X-ray exposure dose when the X-ray exposure dose is oversaturated.

[0043] According to one aspect of this application, a flat panel detector is provided. See also Figure 1 and Figure 2 It includes a flat panel detection module 100 and an image correction module 200.

[0044] The flat panel detection module 100 converts X-rays into electrical signals to generate X-ray images. The image correction module 200 is connected to the flat panel detection module 100 and receives the raw image parameters of the X-ray image and outputs the corrected image parameters of the X-ray image. The flat panel detection module 100 includes a pixel array 110 composed of pixel units 111 and pseudo-pixel units 112. The response sensitivity of the pseudo-pixel units 112 is lower than that of the pixel units 111.

[0045] Each pixel unit 111 and pseudo pixel unit 112 in the pixel array 110 adopts the same design, and each has a TFT switching device and a photodiode device. The entire pixel array 110 is driven by several rows of scan lines. Each scan line is connected to the TFT gate of all pixel units 111 and pseudo pixel units 112 in the corresponding row. The TFT drains of all pixel units 111 and pseudo pixel units 112 in each column are connected to the data lines in the corresponding column to output the electrical signal of the pixel array 110. In addition, the entire pixel array 110 is also connected to the photodiode device of each pixel unit 111 and pseudo pixel unit 112 through a common electrode, thereby providing the same bias potential for each pixel unit 111 and pseudo pixel unit 112.

[0046] As an example, see Figure 2 The pseudo-pixel unit 112 is based on the pixel unit 111, but with an increased area of ​​the incident surface shading layer, reducing the response area of ​​the pixel to a fraction or a tenth of that of the normal pixel unit 111. This reduces the generation of electrical signals and thus reduces the response sensitivity to X-rays. In other words, the response sensitivity of the pseudo-pixel unit 112 to X-rays is only a fraction or a tenth of that of the pixel unit 111. Therefore, even when the exposure dose of X-rays exceeds the saturation dose of the pixel unit 111, it can still provide normal grayscale feedback to the incident X-rays.

[0047] For example, in one implementation, if pixel unit 111 reaches saturation at an X-ray exposure dose of 50 μGy, then when the X-ray exposure dose is 450 μGy, pixel unit 111 will only report a constant saturated grayscale value, and will no longer be able to quantitatively report the true grayscale value at that exposure dose. If the response sensitivity of pseudo pixel unit 112 is set to 1 / 18 of that of pixel unit 111, then the response level at an X-ray exposure dose of 450 μGy is equivalent to the level of normal pixel unit 111 at 25 μGy, far from reaching the grayscale saturation level. In other words, based on the grayscale value reported by pseudo pixel unit 112 and the quantitative relationship between grayscale and exposure dose, the true X-ray exposure dose is calculated, and then the theoretical true grayscale value of normal pixel unit 111 at the current true X-ray exposure dose is calculated in reverse.

[0048] It should be noted that the number of pseudo-pixel units 112 is limited and they are evenly distributed in the pixel array 110. Therefore, after collecting the electrical signals generated by the pseudo-pixel units 112, it is necessary to simulate them to obtain a near-real X-ray exposure dose distribution, thereby improving the accuracy of image correction.

[0049] As an example, see Figure 1The image correction module 200 includes a first correction unit 210 and a second correction unit 220. The first correction unit 210 is used to correct the crosstalk region 320 in the X-ray image, and the second correction unit 220 is used to correct the afterimage region 330 in the X-ray image.

[0050] In this embodiment, see Figure 3 and Figure 4 When the grayscale value of pixel unit 111 exceeds a first threshold, the corresponding X-ray exposure area is designated as the first region 310, i.e., the local high-dose region. The local high-dose region will cause crosstalk and ghosting in the image output by the flat panel detector. The pixel unit 111 in the local high-dose region will interfere with the normal feedback of the grayscale values ​​of the surrounding pixel units 111, thus forming the crosstalk region 320. The interference caused to other pixel units 111 in the horizontal region within this image is called horizontal crosstalk, and the interference caused to other pixel units 111 in the vertical region is called vertical crosstalk. The interference caused by the pixel unit 111 in the local high-dose region to the normal feedback of the grayscale values ​​of the corresponding pixel units 111 in the next frame or several frames of the image also forms the ghosting region 330.

[0051] As an example, the image correction module 200 also includes a data management unit 230, used to receive and store the original image parameters of the X-ray image, including the coordinates of each pixel unit 111 and pseudo pixel unit 112 in each frame and the corresponding grayscale value, as well as the interval time and frame rate of each frame. The first correction unit 210 and the second correction unit 220 obtain the original image parameters through the data management unit 230, and use different algorithms to correct the crosstalk region 320 and / or afterimage region 330 of the X-ray image, thereby outputting the corrected image parameters of the X-ray image.

[0052] Secondly, this application provides a flat panel detector image correction method, which includes using the aforementioned flat panel detector to correct the image output by the flat panel detector.

[0053] First, place the flat panel detector directly facing the X-ray source and use the flat panel detector module 100 to acquire X-ray images;

[0054] Then, the image correction module 200 receives the original image parameters of the X-ray image, performs crosstalk correction and ghosting correction on the X-ray image, and outputs the corrected image parameters.

[0055] As an example, the steps of performing crosstalk correction on an X-ray image using the first correction unit 210 specifically include:

[0056] S11, the data management unit 230 obtains the original image parameters of the X-ray image, including the coordinates and corresponding gray values ​​of each pixel unit 111 in the image, as well as the coordinates and corresponding gray values ​​of the pseudo pixel unit 112.

[0057] S12, mark the first region 310 and the crosstalk region 320 in the X-ray image.

[0058] Based on the coordinates of pixel unit 111 and pseudo pixel unit 112 and their corresponding gray values, the area where the gray value of pixel unit 111 exceeds the first threshold is marked as the first region 310, i.e., the local high dose region. With the first region 310 as the center, the areas where the gray values ​​of pixel unit 111 in the horizontal and vertical directions are disturbed by the first region 310 and the feedback is abnormal are marked as crosstalk regions 320.

[0059] S13, calculate the grayscale correction value of each pixel unit 111 in the crosstalk region 320 based on the grayscale value of each pixel unit 111 in the first region 310.

[0060] A quantitative functional relationship for the grayscale influence value is obtained through theoretical calculations and image patterns. Taking the correction of lateral crosstalk as an example, the coordinates and grayscale value of any pixel unit A in the first region 310 are set as (X,Y,G), and the coordinates and grayscale value of any pixel unit B in the same row as pixel unit A in the lateral crosstalk region 321 are set as (x,Y,g). Then, the grayscale influence value g1=f1(x,g,X,Y,G) of pixel unit A on pixel unit B can be calculated.

[0061] Furthermore, by subtracting the grayscale influence value f1(x,g,X,Y,G) of each pixel unit 111 in the same row within the first region 310 on the grayscale value g of pixel unit B, the grayscale correction value G of pixel unit B can be obtained. B When there are N pixel units 111 in the same row as pixel unit B in the first region 310, then the grayscale correction value of pixel unit B is:

[0062] G B =g-f1(x,g,X1,Y,G1)-f1(x,g,X2,Y,G2)-…-f1(x,g,X N ,Y,G N (1)

[0063] Similarly, if the coordinates and grayscale value of any pixel unit B in the same column as pixel unit A within the vertical crosstalk region 322 are set as (X,y,g), then the grayscale influence value g1 = f1(y,g,X,Y,G) of pixel unit A on pixel unit B can be calculated. Subtracting the grayscale influence value f1(y,g,X,Y,G) of each pixel unit 111 in the same column of the first region 310 on pixel unit B from the grayscale value g of pixel unit B, the grayscale correction value G of pixel unit B can be obtained. B When there are N pixel units 111 in the same column as pixel unit B in the first region 310, then the grayscale correction value of pixel unit B is:

[0064] G B =g-f1(y,g,X,Y1,G1)-f1(y,g,X,Y2,G2)-…-f1(y,g,X,Y N G N (2)

[0065] The first correction unit can calculate the grayscale correction value of each pixel unit 111 in the crosstalk region 320 according to the above equations (1) and (2), and then output the correction parameters of the image crosstalk region 320.

[0066] It should be noted that for the region outside the first region 310 in the X-ray image, the grayscale influence between its pixel units 111 is relatively limited, so the grayscale influence value can be ignored.

[0067] As an example, the steps of using the second correction unit 220 to correct image ghosting on the original image specifically include:

[0068] S21, the data management unit 230 obtains the original image parameters of each frame of X-ray image, including the coordinates and corresponding gray values ​​of each pixel unit 111 in the image, the coordinates and corresponding gray values ​​of the pseudo pixel unit 112, and the frame rate of the X-ray image.

[0069] S22, mark the first region 310 in the X-ray image, and mark the afterimage region 330 in the subsequent M-frame X-ray image.

[0070] Based on the coordinates of pixel unit 111 and pseudo pixel unit 112 and their corresponding gray values, the region where the gray value of pixel unit 111 exceeds the first threshold is designated as the first region 310, i.e., the local high-dose region. The region within the first region 310 where pixel unit 111 interferes with the normal feedback of the gray value of pixel unit 111 at the same position in the next frame or subsequent M frames is designated as the afterimage region 330, where M is a natural number ≥1.

[0071] S23, calculate the grayscale correction value of each pixel unit 111 in the afterimage region 330 using the grayscale value of each pixel unit 111 in the first region 310.

[0072] A quantitative functional relationship for the grayscale influence value is obtained through theoretical calculations and image patterns. For example, if the grayscale value of any pixel unit A within the first region 310 is set to G, and the grayscale value of pixel unit A in the subsequent M-th frame is set to g under the frame rate setting F, then the grayscale influence value of pixel unit A on itself in the subsequent M-th frame can be calculated as g2=f2(F,M,g,G).

[0073] Furthermore, if we want to correct the ghosting of pixel unit A in frame M+1, then we subtract the grayscale influence values ​​of pixel unit A from the first frame to the Mth frame from the grayscale value g of pixel unit A in frame M+1, which is the grayscale correction value G of pixel unit A in frame M+1. A for:

[0074] G A =g-f2(F,M,g,G1)-f2(F,M-1,g,G2)-…-f2(F,1,g,G M (3)

[0075] The second correction unit can calculate the grayscale correction value of each pixel unit 111 in the afterimage region 330 according to the above equation (3), and then output the correction parameters of the image afterimage region 330.

[0076] As an example, the first region 310 includes an unsaturated dose region and / or an oversaturated dose region. The oversaturated dose region is the region where the gray level of pixel unit 111 reaches the gray level saturation value, while the unsaturated dose region is the region where the gray level of pixel unit 111 is between the first threshold and the gray level saturation value.

[0077] When there is an oversaturated dose region in the first region 310, the pixel unit 111 in the oversaturated dose region can only feed back the gray saturation value, and cannot feed back the real gray value according to the actual X-ray incident dose. If the saturated gray value is directly substituted into the above equations (1), (2) and (3), the accurate crosstalk correction parameters and image retention correction parameters cannot be obtained, resulting in the distortion of the output image of the flat panel detector.

[0078] When a pseudo-pixel unit 112 is set in the oversaturated region, the response sensitivity of the pseudo-pixel unit 112 is much lower than that of the pixel unit 111. Based on the gray value fed back by the pseudo-pixel unit 112 and the quantitative relationship between gray value and exposure dose, the true exposure dose of X-rays incident on the pseudo-pixel unit 112 can be calculated. Based on this exposure dose, the theoretical true gray value of other pixel units 111 in the oversaturated region can be simulated and calculated, thereby obtaining more accurate crosstalk correction parameters and image retention correction parameters.

[0079] As an example, the image correction parameters include crosstalk correction parameters and ghosting correction parameters. The crosstalk correction parameter is crosstalk, and the ghosting correction parameter is the grayscale correction value of each pixel unit 111 in the ghosting region 330. The image correction module 200 directly transmits the image correction parameters to an external computer, so that the corrected image can be directly displayed on the image display device.

[0080] This application provides a flat panel detector and its image correction method, including a flat panel detector module 100 and an image correction module 200. The flat panel detector module 100 includes a pixel array 110 composed of pixel units 111 and pseudo-pixel units 112, and the response sensitivity of the pseudo-pixel units 112 is lower than that of the pixel units 111. Under the same exposure dose, the pseudo-pixel unit 112 generates a smaller electrical signal than the pixel unit 111. By utilizing the gray value fed back by the electrical signal of the pseudo-pixel unit 112, and the quantitative relationship between gray value and exposure dose, the true exposure dose of X-rays under oversaturated exposure dose can be calculated, and then the theoretical true gray value of pixel unit 111 under the true exposure dose of X-rays in the same area can be calculated, thereby improving the accuracy of image correction of the flat panel detector.

[0081] The above description is only a preferred embodiment of this application. It should be noted that for those skilled in the art, several improvements and substitutions can be made without departing from the technical principles of this application, and these improvements and substitutions should also be considered within the scope of protection of this application.

Claims

1. A flat panel detector, characterized in that, include: The flat panel detection module is used to convert X-rays into electrical signals to generate X-ray images. An image correction module, connected to the flat panel detection module, is used to receive the original image parameters of the X-ray image and output the corrected image parameters of the X-ray image. The flat panel detection module includes a pixel array composed of pixel units and pseudo-pixel units. The response sensitivity of the pseudo-pixel units is lower than that of the pixel units. Under the same exposure dose, the electrical signal generated by the pseudo-pixel units is smaller than that of the pixel units. By using the gray value fed back by the electrical signal of the pseudo-pixel units and the quantitative relationship between the gray value and the exposure dose, the actual exposure dose of X-rays under the oversaturated exposure dose can be calculated, and then the theoretical true gray value of the pixel units under the actual exposure dose of X-rays in the same area can be calculated.

2. The flat panel detector according to claim 1, characterized in that, The pseudo-pixel units are uniformly arranged in the pixel array.

3. The flat panel detector according to claim 1, characterized in that, The image correction module includes a first correction unit and a second correction unit. The first correction unit is used to correct crosstalk regions in the X-ray image, and the second correction unit is used to correct ghosting regions in the X-ray image.

4. The flat panel detector according to claim 3, characterized in that, The image correction module also includes a data management unit, which receives and stores the original image parameters of the X-ray image. The first correction unit and the second correction unit obtain the original image parameters from the data management unit and use different algorithms to correct the X-ray image, outputting the corrected image parameters of the X-ray image.

5. A method for image correction of a flat panel detector, employing the flat panel detector as described in any one of claims 1 to 4, characterized in that, include: The flat panel detector is placed directly facing the X-ray source, and the X-ray image is acquired using the flat panel detector module. The image correction module receives the original image parameters of the X-ray image, performs crosstalk correction and ghosting correction on the X-ray image, and outputs the corrected image parameters.

6. The image correction method according to claim 5, characterized in that, This includes the step of performing crosstalk correction on the X-ray image using the first correction unit, specifically including: S11, Obtain the raw image parameters of the X-ray image through the data management unit; S12, marking the first region and the crosstalk region in the X-ray image; S13, calculate the grayscale correction value of each pixel unit in the crosstalk region using the grayscale value of each pixel unit in the first region; Wherein, the first region is the region where the gray value of the pixel unit exceeds a first threshold, and the crosstalk region is the region where the gray value of the pixel unit is affected by the first region.

7. The image correction method according to claim 5, characterized in that, This includes the step of using a second correction unit to correct for image retention in X-ray images, specifically including: S21, the raw image parameters of each frame of X-ray image are obtained through the data management unit; S22, mark the first region in the X-ray image, and mark the afterimage region in the subsequent M frames of X-ray images; S23, calculate the grayscale correction value of each pixel unit in the afterimage area using the grayscale value of each pixel unit in the first area; Wherein, the first region is the region where the gray value of the pixel unit exceeds the first threshold, and the afterimage region is the region where the pixel unit in the first region affects the gray value of the pixel unit at the same position in the subsequent M frames of X-ray images.

8. The image correction method according to any one of claims 6 and 7, characterized in that, The first region includes an unsaturated dose region and / or an oversaturated dose region. The oversaturated dose region is the region where the pixel unit reaches a grayscale saturation value, and the unsaturated dose region is the region where the grayscale value of the pixel unit is between a first threshold and a grayscale saturation value.

9. The image correction method according to claim 8, characterized in that, The grayscale value of the pixel unit in the oversaturated dose region is calculated from the grayscale value of the pseudo-pixel unit in the oversaturated dose region.

10. The image correction method according to claim 9, characterized in that, The corrected image parameters include the grayscale correction value of each pixel unit in the crosstalk region and the grayscale correction value of each pixel unit in the afterimage region.

Images