JP2011059058A - Radiographic imaging device - Google Patents

Abstract

[PROBLEMS] To improve mountability to a cassette holder, to suppress deformation of a casing against an external impact force such as when dropped, and to generate rattling of a radiation conversion panel inside the housing due to the impact force. To prevent scratches on the first surface.
A radiographic imaging apparatus includes a first surface that transmits radiation, a second surface as a back surface with respect to the first surface, and an outer peripheral portion of the first surface and an outer peripheral portion of the second surface. And a radiation conversion panel that converts the radiation accommodated in the interior of the housing 34 and transmitted through the first surface 60 into a radiation image. At least one of the first surface 60 (30a), the second surface 86 (32a), and the side surfaces 85 (30a, 32b) before the second surface 86 and the side surface 85 are assembled to form the housing 34. The two surfaces are formed in a convex shape toward the inside of the housing 34.
[Selection] Figure 8

Description

  The present invention relates to a radiographic imaging apparatus in which a radiation conversion panel is accommodated in a housing.

  2. Description of the Related Art In the medical field, a radiographic imaging system that irradiates a subject with radiation and guides the radiation transmitted through the subject to a radiation conversion panel to capture a radiation image is widely used. As the radiation conversion panel, a conventional radiation film in which the radiation image is exposed and recorded, or radiation energy as the radiation image is accumulated in a phosphor and irradiated with excitation light, thereby stimulating the radiation image. A storage phosphor panel that can be extracted as light is known. These radiation conversion panels supply the radiation film on which the radiation image is recorded to the developing device to perform development processing, or supply the storage phosphor panel to the reading device to perform reading processing, A visible image can be obtained.

  On the other hand, in an operating room or the like, it is necessary to be able to immediately read out and display a radiation image from a radiation conversion panel after imaging in order to perform a quick and accurate treatment on a patient. As a radiation conversion panel that can meet such demands, a direct conversion type radiation conversion panel using a solid-state detection element that directly converts radiation into an electrical signal, or a scintillator that temporarily converts radiation into visible light, and the visible light. An indirect conversion type radiation conversion panel using a solid-state detection element that converts light into an electrical signal has been developed. And a radiographic imaging device (radiation detection cassette) is comprised by accommodating the direct conversion type or indirect conversion type radiation conversion panel in a housing | casing.

  In the above radiographic imaging apparatus, a radiation conversion panel, which is a precision electronic device, is housed in a housing. Therefore, in addition to reducing the overall weight and thickness of the apparatus, the rigidity (impact resistance) against external loads accompanying the reduction in thickness is achieved. There is also a demand for suppression of deterioration of the housing and deformation of the housing when a load is applied from the outside (for example, deformation of the housing when dropped).

  In addition, for a conventional radiation detection cassette in which a stimulable phosphor panel is accommodated in a housing, the size of the housing is defined by the JIS (Japan Industrial Standards) standard. A radiation detection cassette in which a direct conversion type or indirect conversion type radiation conversion panel is housed in a housing can be used together with a conventional radiation detection cassette in photographing a subject if the size of the housing can be adapted to the JIS standard. Various devices that have been used can be used as they are.

  In response to such a requirement, Patent Document 1 discloses that an X-ray film is accommodated inside a casing made of carbon fiber groups in which carbon fibers are orthogonally arranged, and the X-ray film is held between a cushion and an intensifying screen. Thus, it has been proposed to improve the deformation and bending strength of the entire apparatus by bringing the X-ray film into close contact with the lid plate and bottom plate constituting the housing.

  Further, in Patent Document 2, a metal plate member is embedded in a resin-made frame portion that constitutes the casing, thereby warping the casing due to molding shrinkage of the frame portion during manufacture of the radiation detection cassette. On the other hand, even when deformation occurs in the casing, the flatness of the entire casing can be maintained by pressing the frame portion in which the metal plate member is embedded. Proposed.

  Further, Patent Document 3 discloses that the entire apparatus is configured by forming only a main member inside the casing by forming a stimulable phosphor layer on a front plate or a back plate made of a highly rigid material by a vapor phase growth method. It has been proposed to reduce the weight of the radiation imaging apparatus and to improve the durability of the radiographic imaging apparatus.

  Furthermore, in Patent Document 4, a radiation conversion panel is attached to a top plate made of a highly rigid material, and the inside of the housing is composed of only main members, thereby reducing the weight of the entire device and against external loads. It has been proposed to jointly suppress deformation (ensure rigidity).

  Furthermore, Patent Document 5 proposes that the side surface of one side of the housing is curved to easily fit the curved side surface to the patient's body.

  Furthermore, in Patent Document 6, saddle-shaped cushion materials whose projecting directions are perpendicular to each other are arranged on the inner surface of the front plate and the inner surface of the back plate, respectively, and the X-ray film is sandwiched between the cushion materials. It has been proposed to realize a substantially circular pressure distribution state centering on the central portion of the radiation detection cassette by closing the front plate and the back plate in the state.

  Furthermore, in Patent Document 7, the radiation incident surface portion of the housing is convex in a direction away from the radiation conversion panel, and is compatible with the radiation detection cassette that houses the stimulable phosphor sheet. A radiation detection cassette containing a direct conversion type or joint conversion type radiation conversion panel has been proposed.

Japanese Utility Model Publication 7-31242 Japanese Patent No. 4266271 JP 2004-212487 A US Patent Application Publication No. 2009/0122959 JP-A-11-160443 JP 59-151148 A JP 2009-103609 A

  By the way, the housing includes a first surface that transmits radiation, a second surface as a back surface with respect to the first surface, and a side surface that connects the outer peripheral portion of the first surface and the outer peripheral portion of the second surface. Composed.

  Here, when the shapes of the first surface, the second surface, and the side surface before constituting the housing are respectively flat, the first surface, the second surface, and the side surface are assembled, and radiation is obtained. When a thin radiographic imaging apparatus is constructed (assembled) by incorporating a conversion panel, the radiographic image after assembly is arranged by placing the radiation conversion panel in close contact with the inner surface of the housing. The imaging device has a shape (convex shape) in which at least one of the first surface, the second surface, and the side surface warps outward in appearance.

  Accordingly, if the first surface and / or the second surface is outwardly convex, the thickness of the housing is increased, so that the radiographic imaging apparatus cannot be inserted into the cassette holder.

  In addition, since the first surface is an irradiation surface (imaging surface) to which radiation is irradiated, if the first surface has an outwardly convex shape, the radiographic image capturing apparatus is inserted into the cassette holder. The first surface and the cassette holder are rubbed (contacted) to form a scratch on the imaging surface. Even when the first surface is in contact with the subject, scratches are formed on the photographing surface by rubbing between the first surface and the subject. Further, when the radiographic imaging device is disposed between the subject and the floor or the bed in order to photograph the subject lying on the floor or the bed, the first surface and the subject, A scratch is formed on the photographing surface by rubbing against the floor or the bed. As a result of the formation of scratches on the imaging surface in this way, the scratches may cause noise in the radiation image.

  Further, when an impact force is applied to the casing from the outside due to dropping or the like, a force for expanding outward is applied to the casing as a whole. This force acts as a force for deforming the casing outward and attempting to disassemble the casing.

  Here, when the first surface, the second surface and / or the side surface is outwardly convex, the force acts on the convex surface as compared with a flat surface or a concave surface. Since the amount of deformation of the housing increases, the radiation conversion panel housed in the housing increases in shakiness, causing the radiation conversion panel to break down.

  However, in the techniques of Patent Documents 1 to 6, since the shapes of the first surface, the second surface, and the side surface before the assembly of the housing are all flat, when the radiation conversion panel is incorporated in the housing, a convex shape is formed. The above surface is formed, and the above-described problems are easily caused. Moreover, in the technique of patent document 7, since the 1st surface is formed in convex shape positively, there exists a possibility of promoting the malfunction mentioned above.

  The present invention has been made in order to solve the above-described problems, and is intended to improve the mounting property to the cassette holder, to suppress the deformation of the housing against an external impact force such as when dropped, and to the impact force. Providing a radiographic imaging apparatus capable of preventing the occurrence of rattling of the radiation conversion panel inside the casing and preventing the occurrence of scratches on the first surface at once. Objective.

In the present invention, a radiographic image capturing apparatus comprises:
A housing composed of a first surface that transmits radiation, a second surface as a back surface with respect to the first surface, and a side surface connecting the outer peripheral portion of the first surface and the outer peripheral portion of the second surface; A radiation conversion panel that converts the radiation contained in the housing and transmitted through the first surface into a radiation image;
In a state before the first surface, the second surface, and the side surface are assembled to form the housing, at least one of the first surface, the second surface, and the side surface is the housing It is characterized in that it is formed in a convex shape toward the inside.

  According to the present invention, the shape of the at least one of the first surface, the second surface, and the side surface before assembling the housing is formed in a convex shape toward the inside of the housing. As a result, when the first surface, the second surface, and the side surface are assembled to form a housing that houses the radiation conversion panel, even if the housing and the radiation conversion panel are in close contact, The shape of the one surface is slightly convex toward the inside of the housing (in terms of appearance, it is concave).

  Thus, if the shape of the first surface, the second surface, and / or the side surface before assembly is convex toward the inside of the housing, the radiation conversion panel is incorporated into the housing. Even when the radiographic imaging apparatus is assembled, the external shape of the housing after assembly does not protrude outward. Therefore, the dimension in the thickness direction of the housing after assembly is stabilized, the radiographic imaging device can be surely inserted into the cassette holder, and the mounting property to the cassette holder is improved. can do.

  Further, if the shape of the first surface, the second surface and / or the side surface before assembly is convex toward the inside of the housing, the shape after assembly faces the inside of the housing. Therefore, even if an impact force is applied from the outside due to dropping or the like, the impact force is applied as compared with the radiographic imaging device of Patent Document 7 in which a convex surface is formed outward. It is possible to reliably suppress deformation of the casing when it is applied, and to reliably prevent the radiation conversion panel from rattling inside the casing due to the impact force.

  Furthermore, if the shape of the first surface before assembly is convex toward the inside of the housing, the shape of the first surface after assembly is slightly convex inward. When the photographing apparatus is inserted into the cassette holder, it is possible to reliably prevent the first surface and the cassette holder from coming into contact (rubbing), thereby avoiding scratches on the first surface. In addition, it is possible to suppress the occurrence of scratches on the first surface due to contact between the first surface and the subject. Furthermore, even if the radiographic imaging device is arranged between the subject and the floor or the bed to photograph a subject lying on the floor or the bed, the first surface, the subject, Generation | occurrence | production of the damage | wound to the said 1st surface by contact with a floor or the said bed can be suppressed reliably. In this way, the occurrence of scratches on the first surface can be effectively prevented, so that it is possible to reliably avoid noise from being mixed into the radiographic image.

  Therefore, according to the present invention, the mounting property to the cassette holder is improved, the deformation of the housing against the impact force from the outside such as when dropped, and the radiation conversion panel inside the housing caused by the impact force. It is possible to realize the prevention of rattling and the prevention of scratches on the first surface at once.

It is a block diagram of the radiographic imaging system concerning a 1st embodiment. It is a perspective view of the radiation detection apparatus of FIG. It is a perspective view for demonstrating the inside of the radiation detection apparatus of FIG. FIG. 4 is a cross-sectional view taken along line IV-IV in FIG. 3. It is a top view which shows arrangement | positioning of an adhesive member. It is a top view which shows arrangement | positioning of a circuit board and a spacer. It is a top view which shows other arrangement | positioning of a circuit board and a spacer. 8A is a cross-sectional view showing the shapes of the first member and the second member before assembling the radiation detection apparatus of FIG. 1, and FIG. 8B is a cross-sectional view showing the shapes of the first member and the second member after assembly. It is. It is a circuit block diagram of the radiation detection apparatus of FIG. It is a block diagram of the radiation detection apparatus of FIG. It is a perspective view for demonstrating charge to the radiation detection apparatus of FIG. It is a perspective view of the radiation detection apparatus which has a handle part. It is a perspective view of the radiation detection apparatus which has a handle part. It is sectional drawing of the radiation detection apparatus which concerns on a 1st modification. It is sectional drawing of the radiation detection apparatus which concerns on a 2nd modification. It is sectional drawing of the radiation detection apparatus which concerns on a 3rd modification. FIG. 17A is a cross-sectional view showing the shapes of the first member and the second member before assembling the radiation detection apparatus according to the fourth modified example, and FIG. 17B shows the shapes of the first member and the second member after assembling. It is sectional drawing shown. FIG. 18A is a cross-sectional view showing the shapes of the first member and the second member before assembling the radiation detection apparatus according to the fifth modification, and FIG. 18B shows the shapes of the first member and the second member after assembling. It is sectional drawing shown. It is sectional drawing of the radiation detection apparatus which concerns on 2nd Embodiment.

  A preferred embodiment of a radiographic imaging apparatus according to the present invention will be described with reference to FIGS.

  First, a radiographic imaging system 10A (hereinafter also referred to as a radiographic imaging system 10A according to the first embodiment) to which a radiation detection apparatus 20A as a radiographic imaging apparatus according to the first embodiment is applied will be described with reference to FIGS. This will be described with reference to FIG.

  As shown in FIG. 1, the radiographic imaging system 10A according to the first embodiment outputs a radiation 12 having a dose according to imaging conditions and irradiates a patient (subject) 16 with a radiation source 14 and a patient 16. A radiation detection device (radiation image capturing device, radiation detection cassette) 20A containing a radiation conversion panel 18 (see FIGS. 3 and 4) that detects the transmitted radiation 12 and converts it into a radiation image, and displays the radiation image. The display device 24 includes a radiation source 14, a radiation detection device 20, and a console (control device) 22 that controls the display device 24.

  Signals are transmitted and received between the console 22 and the radiation source 14, the radiation detection device 20 </ b> A, and the display device 24 by, for example, wired communication using a cable, but UWB (Ultra Wide Band), IEEE 802.11. Of course, signals may be transmitted and received by wireless communication using WiFi (Wireless Fidelity) such as a / g / n or millimeter waves.

  The console 22 is connected to a radiology information system (RIS) 26 that comprehensively manages radiographic images and other information handled in the radiology department in the hospital, and the RIS 26 has medical information in the hospital. Is connected to a medical information system (HIS) 28 for overall management.

  As shown in FIGS. 2 to 4, the radiation detection apparatus 20 </ b> A includes a casing (housing) 34 made of a material that transmits the radiation 12. The casing 34 connects (assembles) the first member 30 constituting the irradiation surface (first surface) 60 of the radiation 12 and the second member 32 constituting the bottom surface (second surface) 86 in the casing 34. Consists of.

  Here, the casing 34 composed of the first member 30 and the second member 32 reduces the overall weight of the radiation detection apparatus 20A and secures rigidity against an external load (for example, a load received from the patient 16). Therefore, it is preferably made of a composite material containing carbon, aramid (aramid fiber) or cellulose microfibril fiber. In this case, the first member 30 and the second member 32 may be made of the same material, or may be made of different materials.

  The casing 34 has an octagonal shape in plan view with corners of the four corners cut off, and each corner has an impact absorbing member made of rubber or the like for absorbing an impact due to an external load. 36 is mounted. In this case, projections 42 and 44 are provided on the corner portion side of the shock absorbing member 36, and the projections 42 are fitted into holes 38 formed in the corner portions of the first member 30, respectively. Each impact absorbing member 36 is mounted on the casing 34 by fitting each projection 44 into a hole 40 formed in each corner of the two members 32. Further, on the side of the second member 32 of the casing 34, a power switch 46 for starting the radiation detection apparatus 20 </ b> A, transmission / reception of signals between the radiation detection apparatus 20 </ b> A and the console 22, and the console 22 are performed. A USB terminal 52 electrically connected to the connector 50 of the USB cable 48 for supplying electric power to the battery 76 in the casing 34 and a card slot 56 for loading the memory card 54 are disposed. .

  As shown in FIGS. 3 and 4, a closed space (chamber 58) is formed in the casing 34 by connecting the first member 30 and the second member 32, and the radiation conversion panel 18 or the like is formed in the chamber 58. The various parts are arranged.

  In the chamber 58, the radiation conversion panel 18 is attached to the irradiation surface 60 to which the radiation 12 is irradiated via an adhesive member (adhesive) 74, while a plurality of spacers 72 are disposed on the bottom surface 86. ing. Further, between the radiation conversion panel 18 and the spacer 72, a heat insulating member 66, a base 68, and a lead sheet 70 are sequentially arranged in a direction from the irradiation surface 60 toward the bottom surface 86. Further, in a space between the spacers 72, a circuit board 90 is attached to a spacer 88 fixed to the base 68, and an electronic component 92 is disposed on the circuit board 90. The electronic component 92 is electrically connected to the radiation conversion panel 18 via the flexible substrate 94.

  As shown in FIG. 3, the chamber 58 is a power source for the radiation detection apparatus 20 </ b> A, a battery 76 that supplies power to each part in the casing 34, and the radiation conversion panel 18 by the power supplied from the battery 76. A cassette controller 78 for driving and controlling a signal including radiation 12 information (radiation image) detected by the radiation conversion panel 18 via a connector 50 and a USB cable 48 electrically connected to the USB terminal 52. A communication unit 80 for transmitting and receiving data to and from 22 is further arranged.

Here, the radiation conversion panel 18 includes a scintillator 64 made of a phosphor based on GOS (Gd ₂ O ₂ S: Tb), CsI: Tl, or the like that once converts the radiation 12 transmitted through the patient 16 into visible light, An array of thin film transistors (TFTs) 100 (see FIG. 9) is formed, and the visible light is formed using a solid state detection element (hereinafter also referred to as a pixel) 102 made of a material such as amorphous silicon (a-Si). Is formed by laminating a photoelectric conversion layer 62 that converts the signal into an electric signal (analog signal).

  In this case, the photoelectric conversion layer 62 is configured by forming a solid-state detecting element 102 by forming a-Si on a glass substrate and forming an array of TFTs 100 by forming electrodes on the glass substrate. The The thickness of the photoelectric conversion layer 62 (the glass substrate constituting the photoelectric conversion layer 62) is thinner than the thickness of the first member 30 and the thickness of the second member 32, and the rigidity of the glass substrate is the same as that of the first member 30 and the first member 30. The rigidity of the two members 32 is lower.

  4 illustrates the configuration of a so-called back-illuminated radiation conversion panel 18 in which the photoelectric conversion layer 62 and the scintillator 64 are stacked in this order on the irradiation surface 60, but the scintillator 64 and the photoelectric conversion layer 62 are not illustrated. Of course, the surface irradiation type radiation conversion panel 18 laminated in order may be used.

  Further, as shown in FIG. 5, among the four side surfaces of the photoelectric conversion layer 62, a plurality of flexible boards 94 are connected to one side surface (the left side surface in FIG. 5) and are orthogonal to the one side surface. A plurality of flexible boards 94 are also connected to the other side surface (the lower side surface in FIG. 5).

  In this case, each flexible substrate 94 connected to the one side surface is provided with a gate line 104 and the like for electrically connecting the TFT 100 (see FIG. 9) and the line scan driving unit 108. Each flexible substrate 94 connected to the other side surface is provided with a signal line 106 and the like for electrically connecting the TFT 100 and the multiplexer 110.

  Therefore, as shown in FIGS. 4 and 6, when the spacer 72 is a cylindrical spacer, each circuit board 90 (the electronic component 92) disposed between the spacers 72 is electrically connected to each flexible board 94. Will be connected. In this case, each flexible board 94 is electrically connected to each circuit board 90 so as to avoid the spacer 72. Thereby, the electronic component 92 can perform an amplification process or the like on the electric signal (analog signal) output from the photoelectric conversion layer 62 via the flexible substrate 94.

  FIG. 6 illustrates the case where the columnar spacers 72 are arranged. However, as shown in FIG. 7, frame-shaped spacers 72 that surround each circuit board 90 may be used. In this case, the frame-shaped spacer 72 is not formed at the location where the flexible substrate 94 is drawn from each circuit board 90.

  Each flexible substrate 94 can electrically connect the battery 76 and the pixel 102 and supply the bias voltage Vb to the pixel 102.

  The adhesive member 74 shown in FIGS. 3 to 5 is made of a material that can transmit the radiation 12 and can be re-peeled, and more preferably, it is made of a material having a transmittance of the radiation 12 of 98% or more. In this case, by disposing a plurality of adhesive members 74 on the upper surface of the photoelectric conversion layer 62, the photoelectric conversion layer 62 can be reliably attached (adhered to) the irradiation surface 60.

  The heat insulating member 66 blocks heat transfer between the radiation conversion panel 18 and the electronic component 92, thereby preventing heat generated in the electronic component 92 from being transferred to the photoelectric conversion layer 62. In addition, since the radiation conversion panel 18 is affixed on the irradiation surface 60 and is hold | maintained in the casing 34, between the radiation conversion panel 18 and the heat insulation member 66 is surface contact like FIG.3 and FIG.4. Or there may be a gap (not shown). If the said clearance gap is provided, the heat insulation effect mentioned above will increase further.

  The lead sheet 70 absorbs the back scattered radiation of the radiation 12 and prevents the radiation 12 transmitted through the patient 16 from being applied to the circuit board 90 and the electronic component 92. In FIG. 4, the lead sheet is disposed on the bottom surface side of the base 68. However, if the lead sheet 70 is interposed between the heat insulating member 66 and the base 68, the radiation 12 to the base 68 is Irradiation can also be avoided.

  The cassette control unit 78 and the communication unit 80 (see FIG. 3) are provided with a lead sheet or the like on the irradiation surface 60 side of the casing 34 in order to avoid damage caused by the irradiation of the radiation 12. Is preferred.

  In addition, the photoelectric conversion layer 62, the scintillator 64, the heat insulating member 66, the base 68, the lead sheet 70, the spacer 72, the spacer 88, and the circuit board 90 described above may be bonded by an adhesive or the like, for example. It may be fastened by an electrically insulating screw member that is not. That is, the photoelectric conversion layer 62, the scintillator 64, the heat insulating member 66, the base 68, the lead sheet 70, the spacer 72, the spacer 88, and the circuit board 90 are accommodated in the chamber 58 of the casing 34 in an integrally configured state. ing.

  Here, as schematically shown in FIG. 8A, the first member 30 and the second member 32 before the casing 34 is configured (assembled) have the same shape.

  That is, the first member 30 has a first plate 30a whose central portion is convex downward in FIG. 8A (convex toward the second member 32), and the outer periphery of the first plate 30a in FIG. 8A. It is comprised from the 1st side wall part 30b projected and formed in the downward direction (direction along the convex shape of the 1st plate 30a). On the other hand, the second member 32 has a central portion convex upward in FIG. 8A (a convex shape on the first member 30 side) and an outer peripheral portion of the second plate 32a in FIG. 8A. It is comprised from the 2nd side wall part 32b projected and formed upwards (direction along the convex shape of the 2nd plate 32a). Therefore, the curvature of the convex portions of the first plate 30a and the second plate 32a before assembly is sufficiently larger than the curvature of the glass substrate constituting the photoelectric conversion layer 62 (see FIGS. 3 and 4).

  Here, the radiation detection apparatus 20A is assembled as follows.

  First, various components such as the radiation conversion panel 18 (see FIGS. 3 and 4) to be incorporated in the casing 34 are arranged between the first member 30 and the second member 32. Specifically, the photoelectric conversion layer 62 is attached to the convex bottom surface of the first plate 30a via the adhesive member 74, and the photoelectric conversion layer 62, the scintillator 64, the heat insulating member 66, and the base that are integrally configured. 68, the lead sheet 70, the spacer 72, the spacer 88, and the circuit board 90, and various components such as the flexible substrate 94 and the electronic component 92 are sandwiched between the first plate 30a and the second plate 32a.

  As described above, the thickness of the glass substrate constituting the photoelectric conversion layer 62 is thinner than the thickness of the first plate 30a, the rigidity of the glass substrate is lower than the rigidity of the first plate 30a, and the glass substrate. Is sufficiently smaller than the curvature of the convex portion of the first plate 30a. Accordingly, when the photoelectric conversion layer 62 is attached to the first plate 30a, the glass substrate is attached to the first plate 30a via the adhesive member 74 in a state of being deformed along the convex bottom surface of the first plate 30a. Attached.

  Next, the front end portion of the first side wall portion 30b and the front end portion of the second side wall portion 32b are connected with an adhesive or the like, or the first side wall portion 30b and the second side wall portion using an engaging member (not shown). The central portion (convex portion) of the first plate 30 a is brought into surface contact with the photoelectric conversion layer 62 while the central portion (convex portion) of the second plate 32 a faces each spacer 72. Make contact.

  As described above, since the photoelectric conversion layer 62, the scintillator 64, the heat insulating member 66, the base 68, the lead sheet 70, and the spacer 72 are integrally formed, the overall thickness of these integrated parts ( The height in the vertical direction in FIG. 4 is maintained at a constant size.

  Therefore, when the convex portion of the first plate 30a comes into surface contact with the photoelectric conversion layer 62, an upward force acts on the convex portion of the first plate 30a from the photoelectric conversion layer 62, so that the first The convex portion of one plate 30a is deformed upward. Further, when the convex portion of the second plate 32a comes into surface contact with each spacer 72, a downward force acts on the convex portion of the second plate 32a from the spacer 72, so that the second plate 32a The convex portion is deformed downward.

  As a result, in the assembled radiation detection apparatus 20A, the shapes of the first plate 30a and the second plate 32a are generally planar (flat) in appearance, as shown in FIG. It is visually recognized as a shape slightly recessed inward of the casing 34 (a shape in which the central portion is slightly convex toward the inside of the casing 34).

  Thus, the first plate 30a having a slightly recessed shape near the center becomes the irradiation surface 60 of the casing 34, and the second plate 32a having a slightly recessed shape near the center is the casing 34. The first side wall portion 30 b and the second side wall portion 32 b become the side surface 85 of the casing 34.

  The thickness in the direction along the first plate 30a and the second plate 32a on the side surface 85 (the first side wall portion 30b and the second side wall portion 32b) is set larger than the thickness of the first plate 30a and the second plate 32a. Has been.

  FIG. 9 is a circuit configuration diagram of the radiation detection apparatus 20A.

  The radiation detection apparatus 20 </ b> A has a structure in which a photoelectric conversion layer 62 in which each pixel 102 made of a substance such as a-Si that converts visible light into an electrical signal is formed is arranged on an array of matrix-like TFTs 100. In this case, in each pixel 102, the charge generated by converting visible light into an electrical signal (analog signal) is accumulated, and the charge can be read out as an image signal by sequentially turning on the TFT 100 for each row. .

  To the TFT 100 connected to each pixel 102, a gate line 104 extending in parallel with the row direction and a signal line 106 extending in parallel with the column direction are connected. Each gate line 104 is connected to a line scan driver 108, and each signal line 106 is connected to a multiplexer 110. Control signals Von and Voff for controlling on / off of the TFTs 100 arranged in the row direction are supplied from the line scanning drive unit 108 to the gate line 104. In this case, the line scan driver 108 includes a plurality of switches SW1 for switching the gate lines 104, and an address decoder 112 that outputs a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 78 to the address decoder 112.

  In addition, the charge held in each pixel 102 flows out to the signal line 106 through the TFTs 100 arranged in the column direction. This charge is amplified by the amplifier 114. A multiplexer 110 is connected to the amplifier 114 via a sample and hold circuit 116. The multiplexer 110 includes a plurality of switches SW2 that switches the signal line 106 and an address decoder 118 that outputs a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 78 to the address decoder 118. An A / D converter 120 is connected to the multiplexer 110, and a radiographic image converted into a digital signal by the A / D converter 120 is supplied to the cassette control unit 78.

  Therefore, in FIG. 9, the line scan driver 108, the multiplexer 110, the amplifier 114, the sample hold circuit 116, and the A / D converter 120 are included in the electronic component 92 (see FIGS. 4, 6, and 7), The flexible substrate 94 includes a portion of the gate line 104 from the line scan driver 108 to the photoelectric conversion layer 62 and a portion of the signal line 106 from the photoelectric conversion layer 62 to the amplifier 114.

  Note that the TFT 100 functioning as a switching element may be realized in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to a gate signal referred to as a TFT.

  As shown in FIG. 10, the cassette controller 78 includes an address signal generator 130, an image memory 132, and a cassette ID memory 134.

  The address signal generator 130 supplies an address signal to the address decoder 112 of the line scan driver 108 (see FIG. 9) and the address decoder 118 of the multiplexer 110. The image memory 132 stores the radiation image detected by the radiation conversion panel 18. The cassette ID memory 134 stores cassette ID information for specifying the radiation detection apparatus 20A.

  The communication unit 80 transmits the cassette ID information stored in the cassette ID memory 134 and the radiation image stored in the image memory 132 to the console 22 from the USB terminal 52 via the connector 50 and the USB cable 48.

  The radiographic imaging system 10A and the radiation detection apparatus 20A according to the first embodiment are basically configured as described above. Next, operations thereof will be described with reference to FIGS. .

  Patient information of the patient 16 to be imaged is registered in advance in the console 22 prior to imaging. If the imaging region and imaging method are determined in advance, these imaging conditions are also registered in advance.

  When taking a radiographic image in an operating room, a medical examination or a round in a hospital, a doctor or a radiographer places the irradiation surface 60 on the radiation source 14 side at a predetermined position between the patient 16 and the bed 96, for example. In this state, the radiation detection apparatus 20A is installed.

  In this case, although the irradiation surface 60 (first plate 30a) and the bottom surface 86 (second plate 32a) of the casing 34 are substantially planar in appearance, the vicinity of the center is slightly on the casing 34 side (inward). The shape is recessed. Therefore, even if the radiation detection apparatus 20A is moved so as to be slid between the patient 16 and the bed 96, the irradiation surface 60 and the patient 16 are rubbed and the irradiation surface 60 is damaged, or the bottom surface 86 and It is possible to avoid scratching the bottom face 86 by rubbing against the bed 96. In addition, even if the patient 16 moves after the radiation detection apparatus 20A is arranged, it is possible to prevent the irradiation surface 60 and the patient 16 from rubbing and scratching the irradiation surface 60.

  Next, the radiation switch 20A is activated by turning on the power switch 46 and supplying power from the battery 76 to each part in the casing 34, and the radiation source 14 is appropriately moved to a position facing the radiation detector 20A. Then, the doctor or the radiographer operates the imaging switch of the radiation source 14 to perform imaging.

  Due to the operation of the imaging switch, the radiation source 14 requests the console 22 to transmit imaging conditions, and the console 22 receives the imaging conditions related to the imaging region of the patient 16 based on the received request. Is transmitted to the radiation source 14. When receiving the imaging conditions, the radiation source 14 irradiates the patient 16 with radiation 12 having a predetermined dose according to the imaging conditions.

  The radiation 12 that has passed through the patient 16 is irradiated to the radiation conversion panel 18, and the scintillator 64 that constitutes the radiation conversion panel 18 emits visible light having an intensity corresponding to the intensity of the radiation 12, thereby configuring the photoelectric conversion layer 62. Each pixel 102 that converts visible light into an electrical signal accumulates it as a charge. Next, the charge information which is the radiation image of the patient 16 held in each pixel 102 is read according to the address signal supplied from the address signal generator 130 constituting the cassette controller 78 to the line scan driver 108 and the multiplexer 110. .

  That is, the address decoder 112 of the line scan driver 108 outputs a selection signal according to the address signal supplied from the address signal generator 130 to select one of the switches SW1, and the TFT 100 connected to the corresponding gate line 104. A control signal Von is supplied to the gates of the two. On the other hand, the address decoder 118 of the multiplexer 110 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 130, sequentially switches the switch SW2, and is connected to the gate line 104 selected by the line scan driving unit 108. The radiographic image as the charge information held in each pixel 102 is sequentially read out via the signal line 106.

  The radiographic image read out from each pixel 102 connected to the selected gate line 104 is amplified by each amplifier 114, sampled by each sample hold circuit 116, and then A / D converter via the multiplexer 110. 120, and converted into a digital signal. The radiographic image converted into the digital signal is temporarily stored in the image memory 132 of the cassette control unit 78.

  Similarly, the address decoder 112 of the line scan driver 108 sequentially switches the switch SW1 in accordance with the address signal supplied from the address signal generator 130, and the charge held in each pixel 102 connected to each gate line 104. A radiation image as information is read out via the signal line 106 and stored in the image memory 132 of the cassette control unit 78 via the multiplexer 110 and the A / D converter 120.

  The radiographic image stored in the image memory 132 is transmitted to the console 22 through the communication unit 80, the USB terminal 52, the connector 50, and the USB cable 48 together with the cassette ID information stored in the cassette ID memory 134. The console 22 performs predetermined image processing on the received radiographic image, and then stores the radiographic image and the cassette ID information after the image processing in association with the registered patient information of the patient 16. The radiographic image subjected to the image processing is transmitted from the console 22 to the display device 24, and the display device 24 displays the radiographic image.

  As described above, according to the radiographic imaging system 10A and the radiation detection apparatus 20A according to the first embodiment, the first plate 30a (irradiation surface 60) and the second plate 32a (bottom surface 86) before the casing 34 is assembled. Is formed in a convex shape toward the inside of the casing 34. Thereby, when the 1st member 30 and the 2nd member 32 are connected and the casing 34 which accommodates the radiation conversion panel 18 grade | etc., Is comprised, the irradiation surface 60 of the casing 34 and the radiation conversion panel 18 are surface contact. Even if the bottom surface 86 and each spacer 72 are in close contact with each other by surface contact, the shapes of the irradiation surface 60 and the bottom surface 86 after assembly are generally flat, but the central portion is inward of the casing 34. It becomes slightly convex toward the surface (concave in appearance).

  Thus, if the shape of the 1st plate 30a and the 2nd plate 32a before an assembly is convex toward the inner side of the casing 34, various components, such as the radiation conversion panel 18, will be integrated in the casing 34, and a radiation detection apparatus. Even when 20A is assembled, the external shape of the assembled casing 34 does not protrude outward. Therefore, the dimension in the thickness direction of the casing 34 after assembly is stabilized, the radiation detection apparatus 20A can be reliably inserted into the cassette holder, and the mounting property to the cassette holder is improved. Can do.

  Moreover, although the shape of the irradiation surface 60 and the bottom surface 86 is substantially flat, the vicinity of the center portion is slightly convex toward the inside of the casing 34, so that impact force is applied to the casing 34 from the outside due to dropping or the like. Even if added, the deformation of the casing 34 when an impact force is applied can be reliably suppressed as compared with the radiation detection device of Patent Document 7 in which a convex surface is formed outward. The occurrence of rattling of various components such as the radiation conversion panel 18 inside the casing 34 due to the force can be reliably prevented.

  As described above, although the shape of the irradiation surface 60 after assembly is substantially planar, the vicinity of the center portion is slightly inwardly convex, so when the radiation detection apparatus 20A is inserted into the cassette holder, By avoiding contact between the irradiation surface 60 and the cassette holder, it is possible to reliably prevent the generation of scratches on the irradiation surface 60. In addition, even when the irradiation surface 60 comes into contact with the patient 16, it is possible to reliably prevent the generation of scratches on the irradiation surface 60 due to contact between the irradiation surface 60 and the patient 16. Further, even if the radiation detection device 20A is disposed between the patient 16 and the floor or bed 96 in order to take an image of the patient 16 lying on the floor or bed 96, the irradiation surface 60, the patient 16, and the Generation | occurrence | production of the damage | wound to the irradiation surface 60 by the contact with the floor or the bed 96 can be prevented reliably. Thus, since the generation | occurrence | production of the damage | wound in the irradiation surface 60 can be prevented effectively, mixing of the noise to a radiographic image can be avoided reliably.

  Furthermore, since the vicinity of the central portion of the irradiation surface 60 and the bottom surface 86 of the radiation detection device 20A is slightly recessed inward of the casing 34, even if a plurality of radiation detection devices 20A are stacked and transported, the irradiation surface 60 ( (Shooting surface) will not be damaged. Moreover, since the dimension of the thickness direction of the casing 34 is stabilized, even if the radiation detection apparatus 20A is stacked and transported, it does not rattle and is easy to transport.

  Therefore, according to the first embodiment, the mounting property to the cassette holder is improved, the deformation of the casing 34 against the impact force from the outside such as when dropped, and the radiation conversion inside the casing 34 due to the impact force. It is possible to prevent the occurrence of rattling of various parts such as the panel 18 and the generation of scratches on the irradiation surface 60 at a time.

  In addition, although 1st Embodiment demonstrated the case where the 1st plate 30a before the assembly and the 2nd plate 32a were formed in convex shape toward the casing 34, it is not limited to this, 1st Even if the side wall part 30b or the second side wall part 32b is formed in a convex shape toward the casing 34, or the front end part of the first side wall part 30b and the front end part of the second side wall part 32b are abutted to form the side surface 85. Even when the side surface 85 is formed in a convex shape toward the casing 34 when formed, the above-described effects can be obtained.

  In the first embodiment, since the radiation conversion panel 18 is attached to the irradiation surface 60 via a plurality of adhesive members 74, the radiation conversion panel 18 and the irradiation surface 60 are integrated to have load resistance. In addition to improving the impact resistance against the fall of the casing 34, it is possible to suppress the deformation of the casing 34 during the drop and the occurrence of a failure of the radiation conversion panel 18 due to the drop.

  In this case, the thickness of the glass substrate of the photoelectric conversion layer 62 is thinner than the thickness of the first plate 30a, the rigidity of the first plate 30a is higher than the rigidity of the glass substrate, and the curvature of the glass substrate is before assembly. Since the curvature of the convex portion of the first plate 30a is sufficiently smaller than the curvature of the first plate 30a, even if the pasting surface of the photoelectric conversion layer 62 on the first plate 30a (the convex bottom surface of the first plate 30a) is curved, By deforming the glass substrate along the convex bottom surface of the plate 30a, the glass substrate can be attached to the first plate 30a via the adhesive member 74.

  Thereby, since the 1st plate 30a (irradiation surface 60) and the photoelectric converting layer 62 are affixed reliably and in the state contact | adhered via the adhesion member 74, the shape of the irradiation surface 60 after an assembly is made into the casing 34 It can be kept slightly convex inward.

  Further, since the adhesive member 74 has a transmittance of the radiation 12 of 98% or more, the presence of the adhesive member 74 can be avoided from affecting the image quality of the radiation image. Further, since the adhesive member 74 can be re-peeled, if the radiation conversion panel 18 breaks down for some reason, the radiation conversion panel 18 is peeled off from the irradiation surface 60 and replaced with a new radiation conversion panel 18 or It is also possible to repair the failed radiation conversion panel 18 and attach it to the irradiation surface 60 again.

  In addition, although 1st Embodiment demonstrated the case where the radiation conversion panel 18 was affixed on the irradiation surface 60 via the adhesion member 74, it is not limited to this, The transmittance | permeability of the radiation 12 of 98% or more is provided. You may affix the radiation conversion panel 18 on the irradiation surface 60 through the adhesive which has. Even in this case, it is needless to say that each effect other than the above-described effect due to the re-peeling can be easily obtained.

  Furthermore, since the 1st member 30 and the 2nd member 32 consist of composite materials containing carbon, an aramid (aramid fiber), or a cellulose microfibril fiber, both weight reduction and ensuring of rigidity of the casing 34 are realizable. In addition, about the 1st member 30 and the 2nd member 32, it is set as the laminated structure (for example, laminate structure of a carbon fiber reinforced plastic and a foam material) of the material mentioned above, and the surface or the inside of the 1st member 30 and the 2nd member 32 By forming a conductive layer, the electromagnetic shielding effect may also be exhibited.

  Furthermore, by inserting a plurality of spacers 72 between the radiation conversion panel 18 and the bottom surface 86, each spacer 72 can be reliably brought into surface contact with the convex portion of the bottom surface 86, and The thickness of the casing 34 can be easily maintained at a constant dimension.

  In addition, by arranging the circuit board 90 and the electronic component 92 in the space between the plurality of spacers 72, the space of the chamber 58 can be used effectively.

  Further, since the heat insulating member 66 is disposed between the circuit board 90 and the electronic component 92 and the radiation conversion panel 18, the heat generated in the electronic component 92 is transmitted to the photoelectric conversion layer 62 and the pixel 102 and the TFT 100. The influence on the operation can be prevented.

  Furthermore, since the lead sheet 70 is disposed between the circuit board 90 and the electronic component 92 and the radiation conversion panel 18, the irradiation of the radiation 12 to the circuit board 90 and the electronic component 92 can be reliably prevented. it can.

  Furthermore, the manufacturing cost of 20 A of radiation detection apparatuses can be reduced by making the 1st member 30 and the 2nd member 32 into the same shape.

  Furthermore, the thickness in the direction along the first plate 30a and the second plate 32a on the side surface 85 (the first side wall portion 30b and the second side wall portion 32b) is thicker than the thickness of the first plate 30a and the second plate 32a. By doing so, the deformation of the corners of the casing 34 due to dropping or the like can be effectively suppressed.

  In addition, since the shock absorbing member 36 is attached to each corner of the casing 34, the shock due to an external load can be reliably absorbed by the shock absorbing member 36.

  Furthermore, by adopting the radiation conversion panel 18 in which the photoelectric conversion layer 62 and the scintillator 64 are laminated, visible light generated by the scintillator 64 can be efficiently converted into an electrical signal (analog signal) by the photoelectric conversion layer 62. As a result, a high-quality radiation image can be obtained.

  In the first embodiment, a radiation image or the like is transmitted from the radiation detection device 20A to the console 22 via the USB cable 48. Instead, a radiation image or the like is transmitted to the memory card 54 loaded in the card slot 56. After recording the above information, the memory card 54 can be taken out and loaded into the console 22.

  In the first embodiment, if signals are transmitted and received by radio communication between the console 22, the radiation detection device 20A, the radiation source 14, and the display device 24, a cable for transmitting and receiving signals is provided. Since it becomes unnecessary, there is no possibility of disturbing the work of a doctor or a radiographer. Therefore, the doctor or radiologist can perform his / her work efficiently. Of course, the wireless communication between the radiation detection apparatus 20A and the external device may be performed by optical wireless communication using infrared rays or the like instead of the communication using the normal radio wave.

  Furthermore, in the first embodiment, a radiographic image is taken due to the operation of the radiographing switch of the radiation source 14 by the doctor or radiographer, but the radiographic image is caused by the operation of the console 22 by the doctor or radiographer. Shooting may be performed.

  Furthermore, in the first embodiment, instead of the above-described configuration, for example, the dose of the incident radiation 12 is directly converted into an electric signal by a photoelectric conversion layer using a solid detection element made of a substance such as amorphous selenium (a-Se). The present invention can also be applied to a direct conversion type radiation detection apparatus that converts to a laser beam.

  The first embodiment can also be applied to a case where a radiation image is acquired using a light readout type radiation detection apparatus. In this light readout type radiation detection apparatus, when radiation enters each solid detection element, an electrostatic latent image corresponding to the dose is accumulated and recorded in the solid detection element. When reading the electrostatic latent image, the radiation conversion panel is irradiated with reading light, and the value of the generated current is acquired as a radiation image. In addition, the radiation conversion panel can erase and reuse a radiation image that is a remaining electrostatic latent image by irradiating the radiation conversion panel with erasing light (see Japanese Patent Application Laid-Open No. 2000-105297).

  Furthermore, when the radiation detection apparatus 20A is used in an operating room or the like, there is a risk that blood or other germs may adhere. Therefore, the radiation detection apparatus 20A has a waterproof and airtight structure and is sterilized and washed as necessary, so that one radiation detection apparatus 20A can be used repeatedly.

  Furthermore, as shown in FIG. 11, it is preferable to place a cradle 140 for charging the battery 76 (see FIGS. 3 and 10) of the radiation detection apparatus 20A at a necessary location in the operating room or hospital. In this case, the connector 142 of the USB cable 48 is connected to the cradle 140, and not only the battery 76 is charged, but also the RIS 26, the HIS 28, the console 22, etc. using the wireless communication function or the wired communication function of the cradle 140. It is also possible to exchange necessary information with an external device. The information to be transmitted / received can include a radiation image recorded in the radiation detection apparatus 20A loaded in the cradle 140.

  In addition, the display unit 144 is disposed on the cradle 140, and the display unit 144 displays necessary information including the charged state of the loaded radiation detection device 20A and the radiation image acquired from the radiation detection device 20A. You may make it make it.

  Further, a plurality of cradles 140 are connected to the network, and the charging states of the radiation detection devices 20A loaded in the respective cradles 140 are collected via the network, and the location of the radiation detection devices 20A in a usable charging state is confirmed. It can also be configured to be able to.

  Furthermore, as shown in FIGS. 12 and 13, handle portions 150 and 160 may be provided on the side portions of the casing 34, respectively.

  In this case, by providing the radiation detection apparatus 20A with the handle portions 150 and 160, the radiation detection apparatus 20A can be easily handled and carried.

  In the radiation detection apparatus 20, guide lines 152 and 162 serving as a reference for the imaging region and the imaging position are formed on the irradiation surface 60 side. By using the guide lines 152 and 162 to position the patient 16 with respect to the radiation detection apparatus 20A and setting the irradiation range of the radiation 12, a radiographic image can be recorded in an appropriate imaging region.

  Display units 154 and 164 for displaying various types of information related to the radiation detection apparatus 20A are disposed outside the imaging region of the radiation detection apparatus 20A. In the display units 154 and 164, the ID information of the patient 16 recorded in the radiation detection apparatus 20A, the number of times the radiation detection apparatus 20A is used, the cumulative exposure dose, and the state of charge of the battery 76 built in the radiation detection apparatus 20A (Remaining capacity), radiographic imaging conditions, positioning image of the patient 16 with respect to the radiation detection apparatus 20A, and the like are displayed. In this case, for example, the radiologist confirms the patient 16 according to the ID information displayed on the display units 154 and 164 and confirms in advance that the radiation detection apparatus 20A is in a usable state. Based on the positioning image, a desired radiographic image of the patient 16 can be positioned in the radiation detection apparatus 20A, and an optimal radiographic image can be captured.

  The radiographic imaging system 10A and the radiation detection apparatus 20A according to the first embodiment are not limited to the above description, and can be changed to various configurations.

  Next, modified examples (first modified example to fifth modified example) of the first embodiment will be described with reference to FIGS.

  As shown in FIG. 14, the first modification is different from the embodiment of FIGS. 1 to 13 in that the radiation conversion panel 18 is directly in surface contact with the irradiation surface 60 without using the adhesive member 74. Different.

  Even in this case, since the radiation conversion panel 18 is in surface contact with the irradiation surface 60, each effect other than the effect related to the adhesive member 74 can be easily obtained.

  As shown in FIG. 15, the second modified example is that the length of the first side wall 30b of the first member 30 is set longer than the length of the second side wall 32b of the second member 32. It differs from the embodiment of FIGS.

  Even in this case, it is possible to easily obtain each effect other than the effect obtained when the first member 30 and the second member 32 have the same shape. Of course, even if the length of the second side wall portion 32b of the second member 32 is made longer than the length of the first side wall portion 30b of the first member 30, the above-described effects can be easily obtained.

  As shown in FIG. 16, in the third modification, the first plate 30a constituting the first member 30 and the first side wall portion 30b are constituted by different members, and the second plate constituting the second member 32. It differs from the embodiment of FIGS. 1-15 by the point by which 32a and the 2nd side wall part 32b are comprised by another member.

  In this case, if the first side wall part 30b and the second side wall part 32b are made of highly rigid members, the load resistance of the radiation detection apparatus 20A can be further improved.

  The first plate 30a and the first side wall portion 30b are configured as separate members, and the second plate 32a and the second side wall portion 32b are the same member, or the first plate 30a and the first side wall portion. Of course, even when 30b is the same member and the second plate 32a and the second side wall portion 32b are formed of different members, the above-described effects of the separate members can be obtained.

  As shown in FIG. 17A, the fourth modified example is that the central portion of the first plate 30a before assembling is convex downward, while the second plate 32a before assembling has a planar shape. 1 to FIG. 16 is different from the embodiment.

  Even in this case, when the casing 34 is assembled by incorporating various components such as the radiation conversion panel 18, the central portion of the irradiation surface 60 is slightly recessed inward of the casing 34, as shown in FIG. Thus, the bottom surface 86 has a planar shape.

  Thereby, each effect by having made the center part of the 1st plate 30a in Drawing 1-Drawing 13 into convex shape below can be acquired easily.

  As shown in FIG. 18A, the fifth modified example is that the first plate 30a before assembly has a planar shape, while the center portion of the second plate 32a before assembly is convex upward. 1 to FIG. 17B are different from the embodiment.

  In this case, when the casing 34 is assembled by incorporating various components such as the radiation conversion panel 18, the irradiation surface 60 has a planar shape as shown in FIG. 18B, while the bottom surface 86 is slightly inward of the casing 34. It becomes a concave shape.

  This prevents rattling when the radiation detector 20A is placed on the bed 96 or the like.

  Next, a radiographic imaging system 10B and a radiation detection apparatus 20B according to the second embodiment will be described with reference to FIG.

  Note that the same components as those in the radiographic imaging system 10A and the radiation detection apparatus 20A (see FIGS. 1 to 18B) according to the first embodiment are denoted by the same reference numerals, and detailed description thereof is omitted.

  In the radiographic imaging system 10B and the radiation detection apparatus 20B according to the second embodiment, instead of the heat insulating member 66, the base 68, and the spacers 72 and 88, a foam member 170 having a heat insulating function and made of an electrically insulating material is used. It differs from the radiographic imaging system 10A and the radiation detection apparatus 20A according to the first embodiment in that they are inserted. That is, the radiation detection apparatus 20A and the radiation detection apparatus 20B have substantially the same shape in appearance, but the configuration in the casing 34 is different from each other.

  In this case, in the radiation detection apparatus 20 </ b> B, the circuit board 90 and the electronic component 92 are built in the foam member 170, and the radiation conversion panel 18, the lead sheet 70, and the foam member 170 are arranged from the irradiation surface 60 toward the bottom surface 86. Arranged in order.

  As a result, the contact area between the foam member 170 and the bottom surface 86 is increased, so that the central portion of the bottom surface 86 can be surely formed into a shape slightly recessed inward of the casing 34.

  Further, since the radiation conversion panel 18, the lead sheet 70 and the foam member 170 are integrated, the dimension in the thickness direction of the casing 34 is further stabilized. The shape can be slightly recessed inward.

  Therefore, according to the second embodiment, each effect of the first embodiment can be made more remarkable.

  Note that the present invention is not limited to the above-described embodiment, and it is needless to say that various configurations can be adopted without departing from the gist of the present invention.

10A, 10B ... Radiation imaging system 12 ... Radiation 14 ... Radiation source 18 ... Radiation conversion panel 20A, 20B ... Radiation detection device 22 ... Console 30 ... First member 30a ... First plate 30b ... First side wall 32 ... Second Member 32a ... 2nd plate 32b ... 2nd side wall 34 ... Casing 58 ... Chamber 60 ... Irradiation surface 62 ... Photoelectric conversion layer 64 ... Scintillator 66 ... Heat insulation member 68 ... Base 70 ... Lead sheet 72 ... Spacer 74 ... Adhesive member 85 ... Side 86 ... Bottom 90 ... Circuit board 92 ... Electronic components

Claims (14)

A housing composed of a first surface that transmits radiation, a second surface as a back surface with respect to the first surface, and a side surface connecting the outer peripheral portion of the first surface and the outer peripheral portion of the second surface;
A radiation conversion panel that is housed in the housing and converts the radiation transmitted through the first surface into a radiation image;
Have
In a state before the first surface, the second surface, and the side surface are assembled to form the housing, at least one of the first surface, the second surface, and the side surface is the housing A radiographic imaging apparatus, characterized by being formed in a convex shape toward the inside. The apparatus of claim 1.
The radiation image capturing apparatus according to claim 1, wherein the radiation conversion panel is in contact with the first surface via an adhesive or an adhesive that can transmit the radiation. The apparatus of claim 2.
The radiation imaging apparatus according to claim 1, wherein the radiation transmittance of the adhesive or the pressure-sensitive adhesive is 98% or more. The apparatus according to claim 2 or 3,
The radiographic image capturing apparatus, wherein the pressure-sensitive adhesive is configured to be removable. In the apparatus of any one of Claims 1-4,
The housing is made of a composite material including carbon, aramid, or cellulose microfibril fiber, and the radiographic image capturing apparatus. In the apparatus of any one of Claims 1-5,
A radiation image capturing apparatus, wherein a spacer or a foam member is interposed between the radiation conversion panel and the second surface. The apparatus of claim 6.
An electronic part for processing the radiation image is disposed in a space between the plurality of spacers in the housing or in the foam member. The apparatus of claim 7.
Between the electronic component and the radiation conversion panel, a heat insulating member for blocking heat transfer between the electronic component and the radiation conversion panel, and / or irradiation of the radiation to the electronic component. A radiographic image capturing apparatus, wherein a shielding member for preventing is arranged. The device according to any one of claims 1 to 8,
The housing includes a first member including the first surface and a first side wall portion projecting from an outer peripheral portion of the first surface toward the second surface, and the second surface and the second surface. A second side wall including a second side wall protruding from the outer periphery toward the first surface;
By connecting the first side wall and the second side wall in a state where the first side wall and the second side wall are opposed to each other, the side surface is configured and the housing is assembled. A radiographic imaging device as a feature. The apparatus of claim 9.
The first member and the second member before assembling the casing have the same shape, and the first surface is formed in a convex shape in a direction in which the first side wall portion projects, and the second surface The radiation image capturing apparatus according to claim 1, wherein the surface is formed in a convex shape in a direction in which the second side wall portion projects. The apparatus of claim 9.
One surface of the first surface and the second surface before assembling the housing is formed in a convex shape in a direction in which a side wall portion connected to the outer peripheral portion of the surface protrudes, and the other surface Is a radiographic imaging device characterized by being formed in a planar shape. The device according to any one of claims 9 to 11,
The first surface and the first side wall portion are constituted by one member or different members,
The radiographic imaging apparatus characterized in that the second surface and the second side wall are made of one member or different members. The apparatus according to any one of claims 9 to 12,
The thickness of the first side wall portion in the direction along the first surface is thicker than the thickness of the first surface,
The radiation image capturing apparatus according to claim 1, wherein a thickness of the second side wall portion in a direction along the second surface is larger than a thickness of the second surface. The device according to any one of claims 1 to 13,
The radiation conversion panel is formed by laminating a scintillator that converts the radiation into visible light and a photoelectric conversion layer that converts the visible light into an electrical signal as the radiation image in a direction along the side surface. ,
When at least the first surface before assembly is formed in a convex shape toward the inside of the housing,
The thickness of the photoelectric conversion layer is thinner than the thickness of the first surface,
The rigidity of the first surface is higher than the rigidity of the photoelectric conversion layer,
The radiographic image capturing apparatus according to claim 1, wherein a curvature of the photoelectric conversion layer is smaller than a curvature of the first surface before assembly.

Images