JP2022142982A - Radiation imaging system, radiation imaging device, and image processing method of radiation imaging system - Google Patents

Abstract

To reduce artifacts generated by a back scattering line caused when a radiation is reflected on a structure such as a wall surface and a floor on a back side of a radiation imaging device.SOLUTION: A radiation imaging system includes: a radiation imaging device having a radiation detection part provided with a plurality of pixels, each of which converts a radiation to an electric signal, and a component disposed on a side opposite to the side where the radiation is made incident of the radiation detection part, which acquires a radiation image based on the radiation emitted by a radiation generation device, passing through a subject, and made incident to the radiation detection part; and an image processing unit for executing acquisition of a correction value for correcting the entering of the component into the radiation image and correction of the radiation image using the correction value.SELECTED DRAWING: Figure 1

Description

The present invention relates to a radiation imaging system, a radiation imaging apparatus, and an image processing method for the radiation imaging system.

BACKGROUND ART Currently, radiation imaging apparatuses using a flat panel detector (hereinafter abbreviated as FPD) made of a semiconductor material as a radiation detection unit are widely used as imaging apparatuses for medical image diagnosis and non-destructive inspection using radiation. there is Such a radiation imaging apparatus is used in a radiation imaging system, for example, in medical image diagnosis as a digital imaging apparatus capable of still image imaging such as general radiography and moving image imaging such as fluoroscopic imaging.

A radiation imaging apparatus generates a radiographic image by converting radiation emitted from a radiation generating apparatus into electrical signals by an FPD arranged inside the radiation imaging apparatus. At this time, part of the irradiated radiation can become scattered radiation (backscattered radiation) that passes through the FPD, is reflected by the structure on the opposite side of the FPD to the incident side of the radiation, and reenters the FPD. Such backscattered rays pass through the components arranged on the side opposite to the radiation incident side of the FPD and enter the FPD. may be lost.

For example, Patent Literature 1 discloses a technique of using an alloy containing Mg and Li, which has high radiation transmittance, on the surface of a housing housing a radiation detector (FPD) opposite to the radiation incident side. disclosed. Radiation that can be arranged between a support that supports the FPD and the FPD in the housing by suppressing backscattered radiation generated by reflection of the radiation on the side of the housing opposite to the side on which the radiation is incident. Artifacts occurring in radiographic images can be reduced while reducing the weight of the shielding plate.

JP 2018-000242 A

However, even if the technique described in Patent Document 1 is used, the radiation that has passed through the housing, the radiation that has passed through the outside of the housing, and the radiation that has not been absorbed by the FPD are the walls and floor on the back side of the housing. It is also possible that backscattered rays are generated by being reflected by other structures. In such cases, it may cause artifacts in radiographic images.

SUMMARY OF THE INVENTION Accordingly, it is an object of the present invention to provide a radiation imaging system capable of reducing artifacts caused by backscattered radiation.

The above-mentioned problem consists of a radiation detection section provided with a plurality of pixels each for converting radiation into an electrical signal, and a component arranged on the opposite side of the radiation detection section from the radiation incident side. a radiographic imaging device for acquiring a radiographic image based on radiation emitted from a radiation generating device and incident on the radiation detection unit after passing through a subject; The problem is solved by a radiation imaging system comprising an image processing unit that acquires a correction value and corrects the radiographic image using the correction value.

According to the present invention, it is possible to provide a radiation imaging system capable of reducing artifacts caused by backscattered radiation.

1 is a diagram showing the configuration of a radiation imaging system according to a first embodiment; FIG. 1 is a diagram showing the configuration of a radiation imaging apparatus 102 according to a first embodiment; FIG. FIG. 4 is a schematic diagram for explaining external scattering according to the first embodiment; 4 is a flowchart showing processing for generating a gain image according to the first embodiment; 4 is a flowchart showing processing from the start to the end of shooting according to the first embodiment; 9 is a flowchart showing processing from the start to end of imaging according to the second embodiment;

Preferred embodiments to which the present invention is applied will now be described in detail with reference to the accompanying drawings. In addition, the following embodiments do not limit the invention according to the scope of claims. Although multiple features are described in the embodiments, not all of these multiple features are essential to the invention, and multiple features may be combined arbitrarily. Furthermore, in the accompanying drawings, the same or similar configurations are denoted by the same reference numerals, and redundant description is omitted. In addition, although the term radiation can typically be X-rays, it is not limited to X-rays, and other radiations (eg, α-rays, β-rays, γ-rays, etc.) can also be applied.

(First embodiment)
FIG. 1 is a diagram showing the overall configuration of a radiation imaging system 10 according to the first embodiment of the invention. The radiation imaging system 10 includes a control device 100 , a radiation generator 101 and a radiation imaging device 102 . The control device 100 includes an imaging condition setting unit 103 , an imaging control unit 104 , an image processing unit 105 and a display unit 106 . A general-purpose computer having a CPU, a main memory, an auxiliary memory, and a display is preferably used for the control device 100, and the functions of each part of the control device 100 are realized.

The radiation generator 101 irradiates the subject P with radiation. The radiation generator 101 is composed of a tube that generates radiation, a collimator that defines the spread angle of the generated radiation beam, and a radiation dosimeter attached to the collimator.

The radiation imaging device 102 generates an image based on the emitted radiation. The generated radiation image is transmitted to the image processing unit 105 . The radiation imaging apparatus 102 also transmits information on the detected radiation dose to the imaging control unit 104 . The internal structure of the radiation imaging apparatus 102 will be described in detail with reference to FIG.

The imaging condition setting unit 103 has imaging condition input means for the operator to input imaging conditions such as tube voltage, tube current, and imaging site. be done. The imaging control unit 104 controls the radiation generation device 101, the radiation imaging device 102, and the image processing unit 105 based on the input imaging conditions.

The image processing unit 105 performs image processing such as offset correction processing, gain correction processing, and noise reduction processing on the radiation image transmitted from the radiation imaging apparatus 102 . The image processing unit 105 transmits the radiographic image after image processing to the display unit 106 . A general-purpose display or the like is used as the display unit 106 and outputs the image information transmitted from the image processing unit 105 .

FIG. 2 is a diagram showing the configuration of the radiation imaging apparatus 102 according to this embodiment. FIG. 2(a) is an external perspective view of the radiation imaging device 102 viewed from the incident surface side, and FIG. 1(b) is a cross-section of the radiation imaging device 102 along line AA shown in FIG. 1(a). is a cross-sectional view seen from the direction of the arrow. An arrow X in FIG. 1B schematically indicates the incident direction of radiation incident on the radiation imaging apparatus 102 .

The radiation imaging apparatus 102 has a substantially rectangular parallelepiped shape, and each component constituting the radiation imaging apparatus 102 is enclosed by a housing 201 . The housing 201 has a front cover 202 and a back cover 203 having a breastplate portion 202a and a frame portion 202b.

The breastplate 202a is a plate-shaped member arranged on the surface of the housing 201 on which radiation is incident. A high-rigidity member is suitable for the chest support 202a because the radiation imaging apparatus 102 may be subjected to a load when it is used for imaging. Moreover, since the breastplate 202a is a surface on which the radiation from the radiation generator 101 is incident, a material with high radiation transmittance is suitable. From these points of view, for example, CFRP (Carbon Fiber Reinforced Plastic) is used for the breastplate 202a. A magnesium alloy is used for the frame portion 202b located on the periphery of the breastplate portion 202a.

The rear cover 203 is a plate-like member arranged on the surface of the housing 201 opposite to the surface on which the radiation is incident. As described above, since a load may be applied to the radiation imaging apparatus 102 , a highly rigid member is suitable for the back cover 203 . In addition, a material with high radiation transmittance is suitable for suppressing reflection of radiation within the housing. From these points of view, for example, CFRP is used for the back cover 203 .

In the housing 201, a shock absorbing sheet 204, a radiation detector 205, and a base 206 are laminated in order from the radiation incident surface side. The shock absorbing sheet 204 protects the radiation detecting section 205 from shocks received from the outside of the housing 201 .

The radiation detection unit 205 consists of a plurality of scintillator crystals that convert the wavelength of radiation into light that can be sensed by the photoelectric conversion elements on a plurality of pixels 205a each having a photoelectric conversion element and arranged in a two-dimensional array. It is an FPD having a scintillator layer 205b. Radiation emitted from the radiation generating device 101 is converted into light by the scintillator layer 205b, and further converted into electrical signals by the photoelectric conversion elements of the plurality of pixels 205a. An electric signal from each pixel of the plurality of pixels 205a is read out by a driving circuit and a readout circuit, and generated as a radiographic image.

The radiation detector 205 is connected to the control board 208 via the flexible circuit board 207 . The control board 208 has the aforementioned driving circuit and reading circuit, and controls driving signals and the like for reading out signals from the photoelectric conversion elements.

The base 206 is a plate-like member for holding the radiation detection unit 205 . A radiation detection unit 205 is disposed on the first surface of the base 206 on which radiation is incident, and a control board 208 and a secondary battery are provided on the second surface, which is the rear surface of the first surface. 209, a wireless module, an antenna section and the like (not shown) are held. A secondary battery 209 supplies driving power. The wireless module and antenna section function as a wireless communication section that wirelessly transmits image signals to an external device.

A radiation shielding material may be provided between the radiation detection unit 205 and a component arranged on the opposite side of the radiation detection unit 205 from the radiation incident side to shield the radiation transmitted backward. good. When a radiation shielding material is provided, materials that absorb radiation such as lead, SUS, (Steel Special Use Stainless), iron, and tungsten are used as the material.

In this embodiment, since the influence of backscattered radiation on the radiographic image can be corrected by an image processing method to be described later, the thickness of the radiation shielding material can be reduced or the radiation shielding material can be eliminated. Therefore, the weight of the radiation imaging apparatus 102 can be reduced.

Next, backscattered radiation, which is a problem in the present invention, will be described with reference to FIG. FIG. 3 is a diagram showing the situation of backscattered rays in the radiation generating apparatus 101 and radiation imaging apparatus 102 in FIG. Radiation emitted from the radiation generating apparatus 101 is incident on a radiation incident surface of a radiation detection unit 205 arranged inside the radiation imaging apparatus 102 .

A portion of the radiation irradiated to the radiation detection unit 205 is transmitted without being absorbed by the scintillator layer 205b of the radiation detection unit 205, and is reflected and scattered by structures such as the wall surface and the floor on the back side of the radiation imaging apparatus 102. and enters from the rear side of the radiation detection unit 205 . Some of the backscattered rays incident from the back side are shielded by the components of the radiation imaging apparatus 102 installed on the back side, and some enter the phosphor. A difference in shadow occurs between a portion shielded by the radiographic image and a portion incident on the radiation detection unit 205, so that parts appear as reflections on the radiographic image, and artifacts occur.

In the present invention, such artifacts due to reflection of parts caused by backscattered rays are reduced by image processing for correcting radiographic images. In the present embodiment, an image processing method for radiographic images that reduces artifacts by adding information about reflected parts to an image (hereinafter referred to as a gain image) for processing (gain correction processing) for correcting the sensitivity of each pixel. will be explained.

FIG. 4 is a flowchart showing processing for generating a gain image according to the first embodiment. In the first embodiment of the present invention, the processing shown in the flowchart of FIG. 4 is performed before the subject P is photographed.

In step S<b>401 , the operator uses the input means installed in the imaging condition setting unit 103 to instruct to start generating a gain image. The instruction is sent to the imaging control unit 104, and the flow moves to step S402.

In step S402, the imaging control unit 104 transmits a dark image acquisition signal to the radiation imaging apparatus 102 in order to acquire a dark image used for offset correction. A dark image is an image based on signals generated in each pixel when no radiation is incident on the radiation imaging apparatus 102 . The dark image is used for processing (offset correction processing) to remove components not based on incident radiation, such as dark current, when generating an image based on radiation incident on the radiation imaging apparatus 102 .

Upon receiving the dark image acquisition signal, the radiation imaging apparatus 102 acquires a signal from each pixel and transmits the signal to the image processing unit 105 . The image processing unit 105 generates a dark image based on the signals from the received pixels, and the flow moves to step S403.

In step S403, an image that is the basis of the gain image is captured. The gain image is obtained by subtracting the dark image acquired in step S402 from the captured image.

First, the imaging control unit 104 transmits a radiation irradiation start signal to the radiation generator 101 . Upon receiving the irradiation start signal, the radiation generating apparatus 101 emits radiation toward the radiation imaging apparatus 102 . Radiation that has reached the radiation imaging apparatus 102 is converted into a dose information signal for each pixel.

After reaching the predetermined irradiation dose, the imaging control unit 104 transmits an irradiation end signal to the radiation generator 101, and the radiation generator 101 stops radiation irradiation. A dose information signal for each pixel is transmitted from the radiation imaging apparatus 102 to the image processing unit 105, and the flow proceeds to step S404.

At this time, the radiation generator 101 is provided with a shield in order to change the radiation quality of the radiation generated from the radiation generator 101 . As the shield, a metal plate made of Al, Cu, or the like is used, which is capable of removing low-energy components from the irradiated X-rays and making the radiation quality high in effective energy. When the effective energy of radiation is high, the amount of radiation that passes through the radiation detection unit 205 increases, so parts are more likely to appear in the captured radiographic image due to backscattered radiation. In the present embodiment, this phenomenon is used to acquire a gain image to which information about reflection of components is added.

In step S404, the image processing unit 105 subtracts the dark image acquired in step S402 from the dose information signal for each pixel received in step S403, and stores the result as a gain image. As described above, the process of generating the gain image, which corresponds to the corrected image of the radiographic image in the present invention, is completed.

Next, the processing from the start to the end of photographing of the subject P according to the first embodiment of the present invention will be described using the flowchart of FIG.

In step S<b>501 , the operator inputs information on the tube voltage, the tube current, and the part to be imaged as imaging conditions by means of the imaging condition input means installed in the imaging condition setting unit 103 . The input imaging conditions are transmitted to the imaging control unit 104 . The imaging conditions are also transmitted by the imaging control unit 104 to the image processing unit 105, and the flow proceeds to step S502.

In step S<b>502 , the imaging control unit 104 transmits a dark image acquisition signal to the radiation imaging apparatus 102 . Upon receiving the dark image acquisition signal, the radiation imaging apparatus 102 acquires a signal from each pixel and transmits the signal to the image processing unit 105 . The image processing unit 105 generates a dark image based on the signals from the received pixels, replaces the dark image saved in step S101, and saves it. After the dark image has been saved, the flow moves to step S503.

In step S503, the imaging control unit 104 controls the radiation generator 101 based on the imaging condition information received in step S501 to start irradiating the subject P with radiation, and the flow proceeds to step S504.

In step S504, the imaging control unit 104 transmits a radiation irradiation start signal to the radiation generation apparatus 101 in order to acquire a radiographic image. Upon receiving the irradiation start signal, the radiation generator 101 irradiates the subject P with radiation. Radiation that has passed through the subject P and entered the radiation imaging apparatus 102 is converted into a dose information signal for each pixel.

After reaching the predetermined irradiation dose, the imaging control unit 104 transmits an irradiation end signal to the radiation generator 101, and the radiation generator 101 stops radiation irradiation. A dose information signal for each pixel is transmitted from the radiation imaging apparatus 102 to the image processing unit 105, and the flow proceeds to step S505.

In step S505, the image processing unit 105 subtracts the dark image acquired in step S502 from the dose information signal for each pixel received in step S504, and the flow proceeds to step S506.

In step S506, the image processing unit 105 performs gain correction processing by dividing the dose information signal for each pixel from which the dark image has been subtracted in step S505 by the gain image acquired in advance in the flow of FIG. . At this time, the reflection of parts is corrected from the dose information signal for each pixel based on the information of the reflection of parts included in the gain image. As soon as the process ends, the flow moves to step S507.

In step S507, the image processing unit 105 performs Log conversion processing on the dose information signal for each pixel on which the gain correction processing has been performed in step S506. As soon as the process ends, the flow moves to step S508.

In step S508, the image processing unit 105 performs processing (noise reduction processing) to reduce noise included in the dose information signal for each pixel after the Log conversion processing has been performed in step S507. conduct. The noise reduction processing is performed based on the information on the tube voltage, the tube current, and the imaged region received by the image processing unit 105 in step S501. As soon as the process ends, the flow moves to step S509.

In step S509, the image processing unit 105 performs processing (gradation processing) for adjusting gradation on the dose information signal for each pixel after the noise reduction processing is performed in step S208. Gradation processing is performed based on the imaging conditions received by the image processing unit 105 in step S501. After completing the processing, the image processing unit 105 transmits the processed signal to the display unit 106, and the flow proceeds to step S510.

In step S510, display unit 106 displays the received information as a two-dimensional image. After display, the flow moves to step S511.

In step S511, the operator determines whether to continue or end shooting. If the operator determines to continue imaging, the flow returns to step S504, and radiation image imaging is performed again. If the operator determines that the shooting is finished, the flow advances to step S512.

In step S<b>512 , the imaging control unit 104 transmits an irradiation end signal to the radiation generator 101 . The radiation generator 101 stops radiation upon receiving the irradiation end signal. With the above, the subject photographing is completed.

In the present embodiment, a shielding object is used to change the quality of the radiation so as to facilitate the occurrence of glare, but the means for facilitating the occurrence of glare is not limited to this.

For example, the area irradiated with radiation from the radiation generating apparatus 101 in obtaining the gain image in step S403 may be wider than the area irradiated in imaging the subject P in steps S503 to S504. In this case, as the amount of radiation passing outside the radiation detection unit 205 increases, the amount of backscattered radiation also increases, making reflection more likely to occur.

Also, the value of the tube voltage set in the radiation generating apparatus 101 in acquiring the gain image performed in step S403 may be set to be larger than the value in imaging the subject P performed in steps S503 to S504, so that radiation with high effective energy can be used. good. In this case, as the amount of radiation transmitted through the radiation detection unit 205 increases, the amount of backscattered radiation also increases, making reflection more likely to occur.

In addition, the difference between the gain-corrected image taken with increased backscatter radiation and the gain-corrected image taken under the same conditions as when the subject was photographed is obtained, and the gain-corrected image is again photographed under the same conditions as when the subject was photographed. You may embed the difference calculated|required by calculation.

(Second embodiment)
Next, a second embodiment of the invention will be described. The difference from the first embodiment is that image processing for correcting reflection of parts is performed using correction values that are artificially created based on arbitrary values. Therefore, in the second embodiment, acquisition of a gain image by radiation through a shield described in the flow of FIG. 4 is not performed, and information for correcting reflection is not included in the gain image.

In the second embodiment, information for obtaining a correction value is acquired before radiographic image capture. Specifically, the positional information of the reflected component, the shape of the edge, and the amount of reflection are given as examples.

These pieces of information can be prepared before taking radiographic images. For example, the position information of the parts that appear in the image is set based on the design information of the radiation imaging apparatus 102 . Also, the shape of the edge of the part to be reflected and the amount of reflection are set based on the image taken in advance. Filtering may also be performed according to, for example, a normal distribution so that the shape of the edge changes gradually.

A correction value is calculated based on these pieces of information, and correction by division is performed for reflections in the captured radiographic image. At least one of these pieces of information is input by the operator using an input device included in the imaging condition setting unit 103 before the subject P is photographed.

Processing from the start to the end of photographing of the subject P according to the second embodiment will be described below with reference to the flowchart of FIG.

Steps S601 to S605 are the same as steps S501 to S505 in the flowchart in FIG.

In step S606, gain correction processing is performed as in the first embodiment, but in the second embodiment, the gain image does not include information for correcting reflection. After the processing ends, the flow moves to step S607.

In step S607, as the reflection correction in this embodiment, reflection correction is performed using an artificially created correction value. When the reflection correction ends, the flow moves to step S608.

Steps S608 to S613 are the same as steps S507 to S51 of the first embodiment. With the above, the subject photographing is completed.

The reflection correction process in step S607 may be performed before the gain correction in step S606. Alternatively, the gain correction image may be multiplied in advance by an artificially created correction image, and the resulting image may be used for the gain correction.

As described above, it is possible to realize a radiation imaging apparatus capable of correcting reflections of parts and structures of the radiation imaging apparatus due to external scattering.

(Other embodiments)
It should be noted that the above-described embodiments of the present invention are merely specific examples of carrying out the present invention, and the technical scope of the present invention is not to be construed in a limited manner. . That is, the present invention can be embodied in various forms without departing from its technical spirit or main features.

For example, in the first and second embodiments, the image processing unit 105 has the function of the control device 100 of the radiation imaging system 10, but the image processing unit 105 is not limited to this. The function 105 may be possessed by the radiation imaging apparatus 102 .

Further, in the present embodiment, the radiation detector 205 is described as a so-called indirect conversion type in which radiation is once converted into visible light and then photoelectrically converted, but it is not limited to this. The radiation detector 205 may employ a so-called direct conversion system that directly converts radiation into charge signals.

Further, in the first and second embodiments, the image processing unit 105 may perform weighting processing on correction values for correcting reflection. For example, for a component whose reflection is to be corrected, the amount of correction may be adjusted by weighting the range in which the component is positioned in the image and other ranges.

The present invention can also be realized by supplying a program that implements the above functions to a system or device via a network or a storage medium, and reading and executing the program by one or more processors in the computer of the system or device. is.

Various recording media such as flexible discs, optical discs (eg CD-ROM, DVD-ROM), magneto-optical discs, magnetic tapes, non-volatile memory (eg USB memory), and ROM can be used as the recording medium. . Alternatively, a program that implements the functions described above may be downloaded via a network and executed by a computer.

Moreover, the functions of the above-described embodiments are not limited to being realized by executing the program code read by the computer. Based on the instructions of the program code, the OS (operating system) running on the computer performs part or all of the actual processing, and the processing realizes the functions of the above-described embodiments. .

Furthermore, the program code read from the recording medium may be written in a memory included in a function expansion board inserted into the computer or a function expansion unit connected to the computer. Based on the instruction of the program code, the CPU or the like provided in the function expansion board or function expansion unit may perform part or all of the actual processing, and the above functions may be realized by the processing.

REFERENCE SIGNS LIST 10 radiation imaging system 101 radiation generator 102 radiation imaging device 105 image processing unit 205 radiation detection unit P subject

Claims (15)

a radiation detection unit provided with a plurality of pixels each for converting radiation into an electrical signal; a radiographic imaging device for acquiring a radiographic image based on radiation emitted from the device and incident on the radiation detection unit after passing through a subject;
an image processing unit that acquires a correction value for correcting reflection of the component in the radiographic image, and corrects the radiographic image using the correction value;
A radiation imaging system comprising: 2. The radiographic imaging system according to claim 1, wherein the image processing unit obtains, as the correction value, a corrected image based on radiation incident on the radiation detection unit without the object being placed. 3. The radiation imaging according to claim 2, wherein the image processing unit acquires the corrected image based on radiation having effective energy higher than that of radiation incident on the radiation detection unit when generating the radiation image. system. 4. The radiation imaging system according to claim 3, wherein the radiation having a high effective energy is generated by shielding the radiation emitted from the radiation generator with a shield. 5. The radiation imaging system according to claim 4, wherein said shield is made of Al or Cu. 6. The image processing unit obtains the corrected image based on the radiation generated by setting the value of the tube voltage of the radiation generating device to be greater than the value for capturing the radiographic image. The radiographic imaging system according to any one of . 7. The radiation according to any one of claims 2 to 6, wherein the image processing unit acquires the corrected image based on radiation in which a radiation-irradiated region is wider than that of the radiographic image. imaging system. 3. The radiation imaging system according to claim 2, wherein the image processing unit acquires the corrected image based on values set based on the information on the component. 9. The radiation imaging system according to claim 8, wherein the information about the part is at least one of position information of the part, shape of an edge of the part, and amount of reflection of the part. 10. A method according to any one of claims 1 to 9, wherein each of said plurality of pixels has a photoelectric conversion element, and said radiation detection section has a scintillator for converting radiation into light detectable by said photoelectric conversion element. 11. The radiographic imaging system according to claim 1. Having a housing that encloses the radiation detection unit and the component,
11. The radiation imaging system according to any one of claims 1 to 10, wherein the surface of the housing opposite to the surface on which radiation is incident is made of CFRP. 12. The radiation imaging system according to any one of claims 1 to 11, wherein no radiation shielding material for shielding radiation is arranged between said radiation detector and said component. a radiation detection unit provided with a plurality of pixels each for converting radiation into an electrical signal; A radiographic imaging device for acquiring a radiographic image based on radiation emitted from the device and incident on the radiation detection unit after passing through a subject,
A radiographic imaging apparatus, comprising: an image processing unit that acquires a correction value for correcting reflection of the component in the radiographic image, and corrects the radiographic image using the correction value. a radiation detection unit provided with a plurality of pixels each for converting radiation into an electric signal; An image processing method for a radiation imaging system having a radiation imaging device for obtaining a radiation image based on radiation emitted from the device and incident on the radiation detection unit after passing through a subject, the method comprising:
an acquisition step of acquiring a correction value for correcting reflection of the component in the radiographic image;
and a correction step of correcting the radiation image using the correction value. A program for causing a computer to execute the image processing method according to claim 14.

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