JP2004212090A - Panel and cassette for shooting radiation image - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To manufacture at a low cost a panel and a cassette for photographing radiation images which have durability. <P>SOLUTION: The panel 30 for photographing radiation images has a structure where a stimulable phosphor layer 32 that consists of stimulable phosphors using alkali halide as a parent body is formed through a vapor phase growth method on the irradiated side of a supporting plate 31 and a heavy metal sheet 33 is located on the side opposite to the irradiated side of the supporting plate 31. Moreover, the panel 30 is accommodated in the cassette 1 for shooting radiation images that has a structure where a back plate 20 holds the side opposite to the stimulable phosphor layer side of the panel 30 and a front plate 10 located on the stimulable phosphor layer side of the panel 30 is provided so that it can freely be attached to and detached from the back plate 20. <P>COPYRIGHT: (C)2004,JPO&NCIPI

Description

[0001]
TECHNICAL FIELD OF THE INVENTION
The present invention relates to a radiographic imaging technique, and more particularly, to a radiographic imaging panel and a radiographic imaging cassette.
[0002]
[Prior art]
2. Description of the Related Art Conventionally, radiation images represented by X-ray images have been used for disease diagnosis and the like. As a method for obtaining such a radiation image, in recent years, a radiation image reading method using a stimulable phosphor has been proposed and put into practical use. In this method, radiation transmitted through a subject is irradiated onto a stimulable phosphor to accumulate radiation energy corresponding to the radiation transmittance of each part of the subject. The radiation energy accumulated by scanning the stimulable phosphor with the stimulating light is emitted as stimulating light, and the stimulable light is converted into an image signal using a photoelectric conversion unit. In addition, a radiation image is obtained as digital image data.
[0003]
The stimulable phosphor used in such a radiation image reading method is provided as a stimulable phosphor layer 3 on the surface of a plastic film 2 by coating or the like, as shown in FIG. What is formed on the stimulable phosphor plate 5 by being sealed with the sealing films 4 and 4 is known. As described above, by stimulating the stimulable phosphor by the sealing film 4 or the like and forming the stimulable phosphor plate 5 on the stimulable phosphor, the stimulable phosphor itself can be easily handled, and a desired arbitrary position can be obtained. By attaching the stimulable phosphor plate 5 to the stimulable phosphor, the stimulable phosphor can be provided at a desired position. Then, the stimulable phosphor plate 5 is adhered to a heavy metal sheet 7 provided on a highly rigid support tray 6 with an adhesive or the like, so that a stimulable phosphor panel 50 used for radiographic imaging is obtained. Is known (for example, see Patent Document 1).
Such a stimulable phosphor panel 50 is, for example, housed in a portable flat housing called a cassette, and is subjected to a predetermined radiation image photographing by a radiation image photographing apparatus. The radiation energy of the radiation transmitted through the subject is recorded on the 50 stimulable phosphor layers 3 as a radiation image.
[0004]
[Patent Document 1]
JP-A-11-249243
[Problems to be solved by the invention]
However, in the case of Patent Document 1, although the stimulable phosphor itself as the stimulable phosphor plate 5 is easy to handle, the stimulable phosphor is sealed with a plurality of films to form the stimulable phosphor. Forming the body plate 5 has a problem in that a complicated manufacturing process is required and the cost is high.
In the stimulable phosphor panel 50 having the above structure, if the sealing film 4 and the plastic film 2 are not used, the stimulable phosphor is provided directly on the heavy metal sheet 7 of the support tray 6. It becomes. However, since the stimulable phosphor and the heavy metal sheet 7 have significantly different coefficients of thermal expansion, the stimulable phosphor is peeled off from the heavy metal sheet 7 due to a temperature change in the use environment of the stimulable phosphor panel. Therefore, such a stimulable phosphor panel has a problem that its durability is inferior.
[0006]
An object of the present invention is to provide a radiation image capturing panel and a radiation image capturing cassette which can be manufactured at lower cost and have durability.
[0007]
[Means for Solving the Problems]
In order to solve the above problems, the invention described in claim 1 is
A support plate,
A stimulable phosphor layer formed on the radiation-irradiated side of the support plate,
A heavy metal sheet disposed on the side opposite to the radiation irradiation side of the support plate,
It is characterized by having.
[0008]
According to the first aspect of the present invention, the stimulable phosphor layer is formed on the radiation-irradiated side of the support plate, and the heavy metal sheet is disposed on the opposite side of the support plate from the radiation-irradiated side. That is, in the radiation image capturing panel, the stimulable phosphor layer is not formed of a heavy metal sheet having a significantly different coefficient of thermal expansion, but is formed on a support plate made of a material having a relatively small difference in coefficient of thermal expansion (relatively small). Have been.
[0009]
Therefore, the radiation image capturing panel in which the stimulable phosphor layer is formed not on the heavy metal sheet but on the support plate, in the use environment, even if there is a temperature change, the stimulable phosphor layer is separated from the support plate. Since it is difficult to peel off, a radiation image capturing panel having durability can be obtained.
In addition, since the stimulable phosphor layer is formed directly on the support plate without using other members, a radiation image capturing panel can be manufactured at a lower manufacturing cost.
[0010]
According to a second aspect of the present invention, in the panel for radiographic imaging according to the first aspect, the stimulable phosphor layer has an alkali halide represented by the following general formula (1) as a base. It is characterized by being made of a phosphor.
General formula: M ¹ X · aM ² X ′ ₂ · bM ³ X ″ ₃ : eA (1)
[Wherein, M ¹ is at least one kind of alkali metal atom selected from atoms of Na, K, Rb and Cs, and M ² is Be, Mg, Ca, Sr, Ba, Zn, Cd, Cu and Ni at least one divalent metal atom selected from atoms of, M ³ is Sc, Y, La, Ce, Pr, Nd, Pm, Sm, Eu, Gd, Tb, Dy, Ho, Er, Tm, Yb, Lu, Al, Ga and In are at least one kind of trivalent metal atom selected from each atom of X, X, X ′ and X ″ are at least one atom selected from each atom of F, Cl, Br and I A is Eu, Tb, In, Cs, Ce, Tm, Dy, Pr, Ho, Nd, Yb, Er, Gd, Lu, Sm, Y, Tl, Na, Ag, Cu, and Mg At least one metal atom selected from the following atoms: , B, e each represent a number between 0 ≦ a <0.5,0 ≦ b <0.5,0 <e ≦ 0.2. ]
[0011]
According to the second aspect of the present invention, the same effect as that of the first aspect of the invention is exerted, and the stimulable phosphor layer is formed of a base material containing an alkali halide represented by the general formula (1). It is formed of a depleted phosphor. Since a stimulable phosphor having an alkali halide as a base has a good radiation (X-ray) absorptance, a highly sensitive stimulable phosphor layer can be formed. Therefore, recording and photographing of a radiographic image with better image quality can be performed.
[0012]
The invention according to claim 3 is the radiation image capturing panel according to claim 1 or 2,
The stimulable phosphor layer is made of a stimulable phosphor having CsBr as a base.
[0013]
According to the third aspect of the present invention, the same effect as the first or second aspect of the invention is exerted, and the stimulable phosphor layer is formed of a stimulable phosphor whose base is an alkali halide CsBr. Therefore, a stimulable phosphor layer with higher sensitivity can be formed. In particular, by precisely forming columnar crystals of CsBr, a stimulable phosphor layer having both high sensitivity and high sharpness can be obtained, and recording and photographing of radiographic images with better image quality can be performed. it can.
[0014]
According to a fourth aspect of the present invention, in the radiation image capturing panel according to any one of the first to third aspects,
The stimulable phosphor layer is made of a stimulable phosphor formed on the support plate by a vapor deposition method.
[0015]
According to the fourth aspect of the invention, the same effect as in the first aspect of the invention is provided, and the stimulable phosphor layer is formed directly on the support plate by a vapor phase growth method. Therefore, the radiation image capturing panel can be manufactured at lower cost without using other members.
In addition, for example, when claim 3 is cited, the columnar crystal of CsBr can be formed with precision control, and the modulation transfer function (MTF) can be improved in the stimulable phosphor layer. . Therefore, a stimulable phosphor layer having both higher sensitivity and higher sharpness can be obtained, and recording and photographing of a radiographic image with better image quality can be performed.
[0016]
The invention according to claim 5 is the radiation image capturing panel according to any one of claims 1 to 4,
The support plate is made of carbon fiber reinforced plastic.
[0017]
According to the fifth aspect of the present invention, the same effect as in the first aspect of the present invention is provided, and the support plate is made of carbon fiber reinforced plastic, so that the rigidity is high. The stimulable phosphor layer is supported by the carbon fiber reinforced plastic, and the stimulable phosphor layer is hardly peeled off from the carbon fiber reinforced plastic which has almost no difference in thermal expansion coefficient (relatively small). It is possible to provide a radiation image capturing panel having a property.
In addition, since the carbon fiber reinforced plastic has heat resistance, for example, even when claim 4 is cited, the stimulable phosphor layer is formed on the support plate by a vapor phase growth method that requires a high temperature. be able to.
[0018]
The invention according to claim 6 is a radiation image capturing cassette including the radiation image capturing panel according to any one of claims 1 to 5,
A back plate that is disposed on the opposite side of the stimulable phosphor layer side of the radiation image capturing panel and holds the radiation image capturing panel,
A front plate that is disposed on the stimulable phosphor layer side of the radiation image capturing panel and is detachably provided on the back plate.
[0019]
According to the invention described in claim 6, the back plate holds the opposite side of the stimulable phosphor layer side of the radiation image capturing panel, and is disposed on the stimulable phosphor layer side of the radiation image capturing panel. Since the front plate is detachably provided on the back plate, the radiation image capturing panel can be accommodated in the radiation image capturing cassette including the back plate and the front plate.
Therefore, by accommodating the radiation image capturing panel in the radiation image capturing cassette, it is possible to protect the panel from shielding external light and to protect the panel from damage due to external factors. When reading a radiation image recorded on the stimulable phosphor layer, the radiation image reading operation must be performed by separating the front plate from the back plate in a predetermined radiation image reading device. Can be.
[0020]
BEST MODE FOR CARRYING OUT THE INVENTION
Hereinafter, an embodiment of the present invention will be described with reference to FIGS.
FIGS. 1 and 2 are views showing an embodiment of a radiation image capturing cassette 1 (hereinafter, cassette 1) according to the present invention. FIG. 1 is a perspective view showing a state where a front plate 10 and a back plate 20 of the cassette 1 are separated, and FIG. 2 is a cross-sectional view showing a state where the front plate 10 and the back plate 20 of the cassette 1 are combined.
[0021]
As shown in FIGS. 1 and 2, the cassette 1 includes a back plate 20 having a radiation image capturing panel 30, a front plate 10 detachably provided on the back plate 20, and the like.
[0022]
As shown in FIG. 2, the radiation image capturing panel 30 includes a support plate 31, a stimulable phosphor layer 32 formed on a surface (surface) of the support plate 31 on the radiation irradiation side, and a support plate 31. And a heavy metal sheet 33 provided on a surface (rear surface) opposite to the radiation irradiation side.
[0023]
The support plate 31 is a plate-like member that supports the stimulable phosphor layer 32 formed on the surface thereof, and is a support that maintains the strength of the radiation image capturing panel 30.
The material of the support plate 31 is, for example, quartz, borosilicate glass, chemically strengthened glass, plate glass such as crystallized glass, cellulose acetate film, polyester film, polyethylene terephthalate film, polyamide film, polyimide film, triacetate film, polycarbonate film, Plastic (resin) films such as syndiotactic polystyrene (SPS) films and the like, carbon fibers, carbon fiber reinforced plastics (CFRP), graphite, DLC and other carbons can be used, and among them, plastic sheets and carbons are preferable. And more preferably a carbon fiber reinforced plastic.
The thickness of the support plate 31 varies depending on its material, material and the like, but is generally 80 μm to 5000 μm, and preferably 250 μm to 4000 μm from the viewpoint of strength and handling.
In the present embodiment, a support plate 31 made of carbon fiber reinforced plastic (CFRP; Carbon Fiber Reinforced Plastics) having high rigidity and heat resistance is used.
[0024]
The stimulable phosphor layer 32 includes a stimulable phosphor on the surface of the support plate 31, particularly a stimulable phosphor based on an alkali halide represented by the general formula (1) in the present embodiment. It is formed to a predetermined thickness by a vapor deposition method (also referred to as a vapor deposition method).
^{Formula; M 1 X · aM 2 X} '2 · bM 3 X''3: eA ····· (1)
[0025]
In the stimulable phosphor represented by the general formula (1), M ¹ is at least one kind of alkali metal atom selected from each of atoms of Li, Na, K, Rb and Cs. Preferably, more preferably, it is Cs.
M ² is at least one divalent metal atom selected from Be, Mg, Ca, Sr, Ba, Zn, Cd, Cu and Ni atoms, and among them, Be, Mg, Ca, Sr and Ba are preferred. .
M ³ is at least one selected from atoms of Sc, Y, La, Ce, Pr, Nd, Pm, Sm, Eu, Gd, Tb, Dy, Ho, Er, Tm, Yb, Lu, Al, Ga and In. It is a kind of trivalent metal atom, and among them, Y, Ce, Sm, Eu, Al, La, Gd, Lu, Ga and In are preferable.
X, X ′, and X ″ are at least one halogen atom selected from F, Cl, Br, and I atoms from the viewpoint of improving the stimulable light emission luminance of the stimulable phosphor. , Cl and Br are preferred, and more preferably Br.
A is at least selected from atoms of Eu, Tb, In, Cs, Ce, Tm, Dy, Pr, Ho, Nd, Yb, Er, Gd, Lu, Sm, Y, Tl, Na, Ag, Cu and Mg. It is one kind of metal atom, and among them, Eu is preferable. These metals are used, for example, as activators.
[0026]
In the stimulable phosphor represented by the general formula (1) stoichiometrically, a, b, and e each represent 0 ≦ a <0.5, preferably 0 ≦ a <0.01, 0 ≦ b <0.5, preferably 0 ≦ b <0.01, 0 <e ≦ 0.2, and preferably 0 <e ≦ 0.1.
[0027]
In particular, in the present embodiment, a stimulable phosphor having CsBr, which is a suitable combination of atoms (M ¹ ; Cs, X; Br) in the aforementioned general formula (1), as a host is used. I do.
[0028]
In addition, as a vapor phase growth method for forming the stimulable phosphor layer 32, a method such as an evaporation method, a sputtering method, a CVD method, or an ion plating method can be used.
In forming the stimulable phosphor layer 32 by the vapor phase growth method, the support plate 31 on which the stimulable phosphor layer 32 is formed is exposed to a high temperature of 100 ° C. or more. Since 31 is made of carbon fiber reinforced plastic and has sufficient heat resistance, the stimulable phosphor layer 32 can be formed by a vapor phase growth method. Further, by controlling the formation of the stimulable phosphor layer 32 by the vapor phase growth method more precisely, the size of the columnar crystal of CsBr of the stimulable phosphor is controlled, and the stimulable phosphor layer is formed. The modulation transfer function (MTF) of the layer 32 can be improved, and the stimulable phosphor layer 32 can achieve both higher sensitivity and higher sharpness.
[0029]
The predetermined thickness of the stimulable phosphor layer 32 varies depending on the intended use of the radiation image capturing panel 30 (cassette 1), but a thickness of 50 μm or more is required to capture a desired radiation image. The thickness is preferably 50 μm to 2000 μm, more preferably 100 μm to 600 μm, and particularly preferably 400 μm to 600 μm.
[0030]
The heavy metal sheet 33 is a sheet-like member formed of a heavy metal such as lead (Pb) or tungsten (W) having a high radiation (X-ray) absorptivity, and an adhesive or a double-sided tape on the back surface of the support plate 31. Affixed. The thickness of the heavy metal sheet 33 is preferably 0.1 mm to 0.3 mm.
The heavy metal sheet 33 shields, among low-energy X-rays (scattered rays) scattered when transmitted through an object such as a subject, those scattered from the back surface side of the support plate 31 toward the stimulable phosphor layer 32, It is a member for removal. That is, the heavy metal sheet 33 shields and removes scattered radiation, thereby preventing a noise image from being recorded on the stimulable phosphor layer 32 due to scattered radiation.
[0031]
As shown in FIG. 2, the back plate 20 includes a back plate rear surface portion 21 and a back plate side surface portion 22 bent at a substantially right angle from the back plate rear surface portion 21 to the front side (front plate 10 side). In addition, an inner wall 23 protruding in the same direction as the back plate side surface portion 22 and a rib 24 are provided on the front surface of the back plate rear surface portion 21.
In addition, a recess 25 is formed in a space surrounded by the back plate rear surface portion 21, the back plate side surface portion 22, and the inner wall 23.
[0032]
The radiation image capturing panel 30 is bonded to the inner wall 23 and the ribs 24 of the back plate 20 via a heavy metal sheet 33 with double-sided tape, an adhesive or the like so that the panel 30 can be replaced.
Thus, the radiation image capturing panel 30 is housed in the back plate 20. In the back plate 20, the cassette 1 is reduced in weight by forming an air layer between the back plate 20 and the radiographic image capturing panel 30 by the ribs 24.
[0033]
The front plate 10 includes a frame 11, a front plate 100 inscribed on the inner surface of the frame 11, and the like.
As shown in FIG. 2, the frame 11 includes a frame front portion 12 facing the front side, and a frame side portion 13 bent from the end of the frame front portion 12 to the rear side (back plate 20 side) substantially at right angles. A frame rear surface portion 14 bent substantially inward in the width direction from the end portion of the frame side surface portion 13, and a bent portion extending from the end portion of the frame rear surface portion 14 toward the frame front portion 12 at a predetermined angle. And a projecting inclined surface portion 15. A light-shielding projection 16 is provided on the rear surface of the frame front portion 12 so as to project in the same direction as the frame side portion 13.
In addition, a concave portion 17 is formed inside the frame 11 by a space surrounded by the frame front portion 12, the frame side portion 13, the inclined surface portion 15, and the light shielding protrusion 16.
[0034]
The frame 11 is, for example, formed by molding a strength material such as aluminum or hard plastic, and is formed of a material that can withstand the load applied to the front plate 10.
The front plate 100 is preferably formed of a member having relatively small radiation absorption, such as aluminum or carbon fiber reinforced plastic.
[0035]
In the cassette 1 thus configured, when the back plate 20 and the front plate 10 are combined as shown in FIG. 2, the light-blocking projections 16 of the front plate 10 enter the recess 25 of the back plate 20 and the recess 17 of the front plate 10 The back plate side part 22 of 20 comes in. With such a structure, the back plate 20 and the front plate 10 are united integrally to constitute the cassette 1, and shield light so that external light does not reach the stimulable phosphor layer 32. Further, for example, a velvet, a sponge, or the like is provided in the concave portion 17 of the front plate 10 or the concave portion 25 of the back plate 20 so that the back plate 20 and the front plate 10 are more closely attached to each other. Can be.
[0036]
In this manner, the front plate 10 and the back plate 20 are separable, and are usually carried in a united state as shown in FIG. 2 to perform radiation imaging or the like. When reading a radiation image recorded on the stimulable phosphor layer 32, the front plate 10 is separated from the back plate 20 in a predetermined radiation image reading device.
[0037]
As described above, in the radiation image capturing panel 30 according to the present invention, an alkali halide (CsBr), which is a stimulable phosphor, is directly adhered to the support plate 31 by the vapor phase growth method, and the stimulable phosphor is formed. Since the layer 32 is formed, a film covering the stimulable phosphor is not required, and a complicated manufacturing process for sealing the stimulable phosphor with the film is not required. Therefore, the radiation image capturing panel 30 and the radiation image capturing cassette 1 can be manufactured at lower manufacturing costs.
The stimulable phosphor layer 32 is formed on a support plate 31 of carbon fiber reinforced plastic, which is a resin having high rigidity. The stimulable phosphor (stimulable phosphor layer 32) and the carbon fiber reinforced plastic Since the difference in the coefficient of thermal expansion from the (support plate 31) is relatively small, deterioration such as peeling of the stimulable phosphor hardly occurs, and since the support plate 31 itself has high rigidity, it is durable. The radiographic image capturing panel 30 and the radiographic image capturing cassette 1 having a property can be provided.
[0038]
In addition, since the heavy metal sheet 33 that shields and removes scattered radiation (X-rays) is provided on the back side of the support plate 31, a noise image due to the scattered radiation from the heavy metal sheet 33 is displayed on the stimulable phosphor layer 32. Can be prevented from being recorded.
[0039]
In the above-described embodiment, the heavy metal sheet 33 is made of a heavy metal such as lead (Pb) or tungsten (W) having a high X-ray absorptivity, but the present invention is not limited to this. Instead, a sheet having a radiation shielding function by kneading a metal powder into a polymer resin (for example, a heavy metal sheet manufactured by Sumitomo Electric Co., Ltd., or a Kanebo high specific gravity resin manufactured by Kanebo Gosen Co., Ltd.) may be used.
[0040]
In addition, it goes without saying that specific detailed structures and the like can be appropriately changed.
[0041]
【The invention's effect】
The stimulable phosphor layer in the radiation image capturing panel according to the present invention is not a heavy metal sheet having a significantly different coefficient of thermal expansion, but a support plate made of a material having little (relatively small) difference in coefficient of thermal expansion. Since the stimulable phosphor layer and the support plate may each undergo thermal expansion due to a temperature change, there is almost no difference in the coefficient of thermal expansion between the stimulable phosphor layer and the support plate. Therefore, distortion does not easily occur, and the stimulable phosphor layer hardly peels off from the support plate. Therefore, a radiation image capturing panel having durability can be obtained.
Further, since the stimulable phosphor layer is formed directly on the support plate by a vapor deposition method or the like without using other members, a radiation image capturing panel can be manufactured at a lower manufacturing cost.
[0042]
In addition, a highly stimulable phosphor layer is formed by using a stimulable phosphor having an excellent radiation (X-ray) absorptivity as a base, particularly CsBr, for forming the stimulable phosphor layer. can do. Therefore, a radiographic image capturing panel capable of recording and capturing a radiographic image with better image quality can be provided.
[0043]
The same effect can be obtained in a radiation image capturing cassette including such a radiation image capturing panel.
[Brief description of the drawings]
FIG. 1 is a perspective view of a radiation image capturing cassette according to the present invention when a front plate and a back plate are separated.
FIG. 2 is a cross-sectional view of the radiation image capturing cassette according to the present invention when a front plate and a back plate are integrated.
FIG. 3 is a cross-sectional view of a conventional stimulable phosphor panel (panel for radiographic image capturing).
[Explanation of symbols]
DESCRIPTION OF SYMBOLS 1 Radiation imaging cassette 10 Front plate 20 Back plate 30 Radiation imaging panel 31 Support plate 32 Stimulable phosphor layer 33 Heavy metal sheet

Claims (6)

A support plate,
A stimulable phosphor layer formed on the radiation-irradiated side of the support plate,
A heavy metal sheet disposed on the side opposite to the radiation irradiation side of the support plate,
A radiation image capturing panel comprising: The radiation image capturing panel according to claim 1, wherein the stimulable phosphor layer is formed of a stimulable phosphor having an alkali halide represented by the following general formula (1) as a base.
General formula: M ¹ X · aM ² X ′ ₂ · bM ³ X ″ ₃ : eA (1)
[Wherein, M ¹ is at least one kind of alkali metal atom selected from atoms of Na, K, Rb and Cs, and M ² is Be, Mg, Ca, Sr, Ba, Zn, Cd, Cu and Ni at least one divalent metal atom selected from atoms of, M ³ is Sc, Y, La, Ce, Pr, Nd, Pm, Sm, Eu, Gd, Tb, Dy, Ho, Er, Tm, Yb, Lu, Al, Ga and In are at least one kind of trivalent metal atom selected from each atom of X, X, X ′ and X ″ are at least one atom selected from each atom of F, Cl, Br and I A is Eu, Tb, In, Cs, Ce, Tm, Dy, Pr, Ho, Nd, Yb, Er, Gd, Lu, Sm, Y, Tl, Na, Ag, Cu, and Mg At least one metal atom selected from the following atoms: , B, e each represent a number between 0 ≦ a <0.5,0 ≦ b <0.5,0 <e ≦ 0.2. ] The radiation image capturing panel according to claim 1, wherein the stimulable phosphor layer is made of a stimulable phosphor having CsBr as a base. 4. The radiation image capturing apparatus according to claim 1, wherein the stimulable phosphor layer is formed of a stimulable phosphor formed on the support plate by a vapor deposition method. 5. panel. The panel for radiographic imaging according to any one of claims 1 to 4, wherein the support plate is made of carbon fiber reinforced plastic. A radiographic imaging cassette comprising the radiographic imaging panel according to any one of claims 1 to 5,
A back plate that is disposed on the opposite side of the stimulable phosphor layer side of the radiation image capturing panel and holds the radiation image capturing panel,
A front plate disposed on the stimulable phosphor layer side of the radiation image capturing panel and detachably provided on the back plate.

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