JP2021105538A - Radiographic device - Google Patents

Abstract

To provide a radiographic device which allows a capacitor for supplying sufficient power to be provided inside while maintaining the improvement of portability.SOLUTION: A recess part 1831 dented toward a capacitor 130 is formed at a housing 180 and at least a part of the recess part 1831 is formed in a manner to be superimposed on a main body part 131 of the capacitor 130 when viewed from a direction (X direction) orthogonal to an incident direction (Z direction) of a radiation R. At least a part of a sealing part 132 of the capacitor 130 is arranged between the recess part 1831 and a radiation detection panel 110 in the incident direction (Z direction) of the radiation R.SELECTED DRAWING: Figure 2

Description

The present invention relates to a radiographic apparatus having a radiation detection panel for detecting incident radiation.

Radiation imaging devices that obtain radiographic images by detecting the intensity distribution of radiation that has passed through the subject to be imaged are widely and generally used in industrial non-destructive inspection and medical diagnosis. In such a radiography apparatus, an apparatus has been developed in consideration of portability and operability in order to enable rapid and wide-ranging imaging of a wide range of subjects. For example, in order to improve the portability of the radiographic imaging apparatus, a radiographic imaging apparatus having a built-in or removable state of a rechargeable battery as a power source for supplying electric power has also been proposed. For example, Patent Document 1 describes an example in which a capacitor is configured as a power source to secure electric power required for a radiography apparatus. Further, for example, Patent Document 2 proposes a radiography apparatus in which a concave portion (grip portion) for gripping is formed in an outer housing in order to improve portability.

Japanese Unexamined Patent Publication No. 2012-237692 JP-A-2017-67564

However, for example, in the capacitor described in Patent Document 1, in order to supply sufficient electric power, a corresponding volume of the capacitor is required, and it occupies a limited volume inside the radiography apparatus. On the other hand, in order to improve portability, if a grip portion recessed toward the inside is provided, for example, the housing of the radiography apparatus described in Patent Document 2, the internal volume of the radiography apparatus is reduced. It will be. That is, in the conventional radiography apparatus, it has been a problem to be able to arrange a capacitor that supplies sufficient power inside while maintaining the improvement of portability.

The present invention has been made in view of such a problem, and it is intended to provide a radiography apparatus capable of arranging a capacitor that supplies sufficient power inside while maintaining improved portability. The purpose.

The radiography apparatus of the present invention includes a radiation detection panel for detecting incident radiation, a capacitor for supplying power to the radiation detection panel, and a housing including the radiation detection panel and the capacitor. The capacitor includes a main body portion formed by stacking electrodes, a sealing portion that seals the periphery of the main body portion, and a terminal portion for electrically connecting to an external constituent portion of the capacitor. , And the housing is formed with recesses recessed toward the capacitor, and at least a part of the recesses is viewed from a direction orthogonal to the incident direction of the radiation. It is formed so as to overlap the main body portion, and at least a part of the sealing portion or the terminal portion is arranged between the recess and the radiation detection panel in the incident direction of the radiation.

According to the present invention, a capacitor that supplies sufficient power can be arranged inside while maintaining the improvement in portability of the radiography apparatus.

It is external perspective view of the radiological imaging apparatus which concerns on 1st Embodiment of this invention. It is a figure which shows an example of the internal structure of the radiographing apparatus which concerns on 1st Embodiment of this invention in the I-I cross section shown in FIG. 1 (b). It is a figure which shows 1st Embodiment of this invention and shows an example of the schematic structure of the capacitor of FIG. It is a figure which shows an example of the internal structure when the radiographing apparatus which concerns on 1st Embodiment of this invention shown in FIG. 2 is seen from the back side of the housing. It is a figure which shows an example of the internal structure of the radiography apparatus which concerns on the 2nd Embodiment of this invention in the I-I cross section shown in FIG. 1 (b). It is a figure which shows an example of the internal structure of the radiographing apparatus which concerns on 3rd Embodiment of this invention in the I-I cross section shown in FIG. 1 (b). It is a figure which shows an example of the internal structure of the radiography apparatus which concerns on other embodiment of this invention in the I-I cross section shown in FIG. 1 (b).

Hereinafter, embodiments (embodiments) for carrying out the present invention will be described with reference to the drawings. However, the details of the dimensions and the structure shown in each embodiment of the present invention described below are not limited to the contents described in the specification and the drawings. Further, in the present specification, the radiation according to the present invention is not limited to X-rays, but also includes α-rays, β-rays, γ-rays, particle beams, cosmic rays and the like.

(First Embodiment)
First, the first embodiment of the present invention will be described.

FIG. 1 is an external perspective view of the radiography apparatus 100 according to the first embodiment of the present invention. Specifically, FIG. 1A is an external perspective view of the exterior housing of the radiation photographing apparatus 100 as viewed from the side of the incident surface 181 on which radiation is incident. Further, FIG. 1B is an external perspective view of the exterior housing of the radiography apparatus 100 as viewed from the back surface 183 located on the side opposite to the incident surface 181 shown in FIG. 1A. Further, FIGS. 1A and 1B also show a side surface 182 connecting the incident surface 181 and the back surface 183. Further, as shown in FIG. 1B, a recess 1831 recessed toward the inside of the radiography apparatus 100 is formed on the back surface 183 in order to improve the portability of the radiography apparatus 100.

FIG. 2 is a diagram showing an example of the internal configuration of the radiography apparatus 100 according to the first embodiment of the present invention in the I-I cross section shown in FIG. 1 (b). In the following description, the radiography apparatus 100 according to the first embodiment shown in FIG. 2 will be described as "radiography apparatus 100-1". Further, in FIG. 2, an XYZ coordinate system in which the radiation incident direction in which the radiation R indicated by the dotted arrow is incident is the Z direction, and the directions orthogonal to the Z direction and orthogonal to each other are the X direction and the Y direction. Is illustrated.

As shown in FIG. 2, the radiography apparatus 100-1 includes a radiation detection panel 110, a support base 120, a capacitor 130, a connection wiring 140, a control board 150, a flexible circuit board 160, a buffer member 170, and a housing 180. It is configured to have.

The radiation detection panel 110 is a component that detects the incident radiation R (including the radiation R that has passed through the subject H) emitted by a radiation generator (not shown). Specifically, the radiation detection panel 110 converts the incident radiation R into a radiation image signal which is an electric signal according to the intensity thereof. The radiation detection panel 110 is formed from, for example, a sensor substrate on which a plurality of (many) photoelectric conversion elements (sensors) are arranged, a phosphor layer (scintillator layer) arranged on the sensor substrate, a phosphor protective film, and the like. It is a so-called indirect conversion type radiation detection panel. At this time, the phosphor layer (scintillator layer) converts the incident radiation R into visible light, and the plurality of photoelectric conversion elements convert the visible light into a radiation image signal which is an electric signal. Further, the phosphor protective film is made of a film having low moisture permeability and is used to protect the fluorescent substance. The radiation detection panel 110 is connected to the flexible circuit board 160. In the present embodiment, the radiation detection panel 110 is a so-called direct conversion type radiation detection panel composed of a conversion element made of a-Se or the like and a conversion element portion in which electric elements such as a TFT are arranged two-dimensionally. It may be. Further, the material of the sensor substrate of the radiation detection panel 110 may be glass or the like, but a highly flexible resin or the like may be used, and the material is not limited thereto.

The support base 120 is a component that supports the radiation detection panel 110.

The capacitor 130 is a power supply device for supplying electric power necessary for operation to the radiation detection panel 110, the control board 150, the flexible circuit board 160, and the like, and is a component that can be charged and discharged in a short time.

Here, the schematic configuration of the capacitor 130 will be described with reference to FIG.
FIG. 3 is a diagram showing a first embodiment of the present invention and showing an example of a schematic configuration of the capacitor 130 of FIG. Specifically, FIG. 3A is a diagram showing an example of the external configuration of the capacitor 130 of FIG. 2, and FIG. 3B is a diagram in the II-II cross section shown in FIG. 3A. It is a figure which shows an example of the schematic structure of the capacitor 130 of 2. Here, in FIG. 3, the same reference numerals are given to the configurations similar to those shown in FIG.

As shown in FIG. 3 (the same applies to FIG. 2), the capacitor 130 includes a main body 131 formed by stacking electrodes, a sealing portion 132 that covers and seals the periphery of the main body 131, and the capacitor 130. It is configured to include a terminal portion 133 for electrically connecting to an external component portion of the above. Here, among the configurations of the capacitor 130 shown in FIG. 3A, as shown in FIG. 3B (the same applies to FIG. 2), the main body 131 is generally the thickest. As shown in FIGS. 2 and 3, the capacitor 130 has a sealing portion 132 for safety, and the terminal portion 133 is connected to a connection wiring 140 such as a lead wire by using screws or solder. Need to connect. For these reasons, a large amount of space is required when mounting the capacitor 130 on the radiography apparatus 100-1. Since the terminal portion 133 of the capacitor 130 serves as an electrical connection portion, in order to improve robustness, it is protected from contact with other structures when an external force is applied to the radiographing apparatus 100-1. Or, it is conceivable to provide a space around the terminal portion 133. Further, the capacitor 130 can be mounted by a lithium ion capacitor or the like.

In general, when the capacity of the secondary battery is improved, the operator can take many pictures with one charge when using the battery. However, in order to improve the capacity of the capacitor 130, it is necessary to increase the volume of the capacitor 130 as well. In addition to the radiation detection panel 110 and the capacitor 130, which is a secondary battery, other structures such as the control board 150 need to be arranged inside the housing 180 of the radiography apparatus 100-1. Further, the radiography apparatus 100-1 requires sufficient strength because it is conceivable that the subject H, such as a patient, takes an image while applying a load. Therefore, ribs, bosses, and the like are generally formed from the support base 120, which is a structural material, and the back surface 183 of the housing 180, in order to improve the strength of the radiography apparatus 100-1. It is necessary to arrange structural materials and electrical parts in the limited volume inside the body 180.

As described above, the volume of the internal space of the housing 180 of the radiography apparatus 100-1 is limited, but the volume of the capacitor 130 is also required to supply sufficient power, and the capacitor 130 is sealed. Due to the presence of the portion 132 and the terminal portion 133, the mounting volume becomes larger. On the other hand, if the recess 1831 is formed in the housing 180 in order to improve the portability (operability) of the radiography apparatus 100-1, the limited volume inside the housing 180 will be further reduced. , It is necessary to use the internal space of the housing 180 more efficiently. Therefore, in the present embodiment, as shown in FIG. 2, at least a part of the recess 1831 is the main body of the capacitor 130 when viewed from the direction (X direction) orthogonal to the incident direction (Z direction) of the radiation R. It is formed so as to overlap the portion 131, and at least a part of the sealing portion 132 of the capacitor 130 is a recess 1831 (more specifically, a radiation detection panel 110 of the recess 1831) in the incident direction (Z direction) of the radiation R. A capacitor 130 is provided in the housing 180 by arranging it between the radiation detection panel 110 and (the most recessed portion toward the) and supplying sufficient power while maintaining the improved portability of the radiography apparatus 100-1. It is designed so that it can be efficiently placed in the limited space inside.

Further, since the terminal portion 133 of the capacitor 130 is connected to the connection wiring 140 such as a lead wire by a screw or solder, a space is required. In the present embodiment, at least one terminal portion 133 of the capacitor 130 (terminal portion 133 located at the left end in FIG. 2) is a radiographing apparatus rather than the recess 1831 when viewed from the incident direction (Z direction) of the radiation R. It is located outside 100-1. Further, when viewed from the incident direction (Z direction) of the radiation R, the main body 131 of the capacitor 130 has at least one terminal 133 having a recess 1831 in between (terminal 133 located at the left end in FIG. 2). It is located on the opposite side of. With this arrangement configuration, when an external force (impact) is applied to the radiography apparatus 100-1, the terminal portion 133 arranged on the outside of the housing 180 is sandwiched between the side surface 182 of the housing 180 and the recess 1831. Since it is arranged at a position, the housing 180 is arranged at a place where there is little deformation. Therefore, the terminal portion 133 has a structure that can be easily protected against an external force (impact).

Next, the description of the other components shown in FIG. 2 will be started.
The connection wiring 140 is wiring for electrically connecting the capacitor 130 (more specifically, the terminal portion 133 of the capacitor 130) and the control board 150 or the like.

The control board 150 uses, for example, an electric board for controlling the operation of the radiation detection panel 110, an electric board for reading a radiation image signal which is an electric signal converted by the radiation detection panel 110, and a read radiation image signal. Includes electrical substrates and the like to be processed (eg, generate image data of radiographic images). The radiographic image signal (image data of the radiological image) obtained by the control board 150 is transferred to the outside of the radiographic imaging apparatus 100-1, displayed on a monitor or the like, and used for diagnosis or the like.

The flexible circuit board 160 is a circuit board that electrically connects the radiation detection panel 110 and the control board 150. Specifically, one end of the flexible circuit board 160 is connected to the radiation detection panel 110, and the other end is connected to the control board 150.

The cushioning member 170 is arranged between the housing 180 (more specifically, the incident surface 181 of the housing 180) and the radiation detection panel 110, and is a member that protects the radiation detection panel 110 from external forces and the like. The buffer member 170 is preferably made of, for example, a foamed resin or a gel.

As described with reference to FIG. 1, the housing 180 includes an incident surface 181 and a side surface 182 and a back surface 183. The housing 180 is a component that includes a radiation detection panel 110, a support base 120, a capacitor 130, a connection wiring 140, a control board 150, a flexible circuit board 160, and a buffer member 170. Further, a recess 1831 recessed toward the capacitor 130 is formed on the back surface 183 of the housing 180. At this time, if the recess 1831 is deeply recessed toward the radiation detection panel 110, the operator can perform stable handling and the rigidity of the housing 180 is improved. However, the deeper the recess, the more radiation is emitted. The internal volume of the photographing apparatus 100-1 will be reduced.

FIG. 4 is a diagram showing an example of an internal configuration of the radiography apparatus 100-1 according to the first embodiment of the present invention shown in FIG. 2 when viewed from the back surface 183 side of the housing 180. In FIG. 4, the same reference numerals are given to the configurations similar to those shown in FIGS. 2 and 3, and detailed description thereof will be omitted. Further, FIG. 4 illustrates an XYZ coordinate system corresponding to the XYZ coordinate system shown in FIG.

In the example shown in FIG. 4, the radiographing apparatus 100-1 is configured to have a plurality of capacitors 130 arranged along a direction (Y direction) orthogonal to the Z direction which is the incident direction of the radiation R. ing. Specifically, in the example shown in FIG. 4, as a plurality of capacitors 130, two capacitors 130, the first capacitor 130-1 and the second capacitor 130-2, are viewed from the Z direction, which is the incident direction of the radiation R. Sometimes they are arranged almost parallel. In the case of the example shown in FIG. 4, as can be seen from FIGS. 2 and 1, the recess 1831 is the first capacitor 130- which is a plurality of capacitors 130 when viewed from the incident direction (Z direction) of the radiation R. It is formed at a position overlapping the first and second capacitors 130-2. At this time, the recess 1831 may be formed so as to overlap the two capacitors 130 shown in FIG. 4 and to be long in the arranged direction. In the example shown in FIG. 1B, a part of the recesses 1831 are arranged long along the outer shape of the radiography apparatus 100 in this way. As a result, by forming the recess 1831 large, the space gripped by the operator can be widened, which leads to improvement in maneuverability. The recess 1831 is not limited to the arrangement shown in FIG. 1B. For example, the recess 1831 is formed so as to be continuous around the outer shape of the radiographing apparatus 100 when viewed from the incident direction of the radiation R. May be good.

Further, in FIG. 4, similarly to FIG. 2, the capacitor 130, the control board 150, and the flexible circuit board 160 are arranged along the X direction, and these are arranged on the support base 120.

Each of the plurality of capacitors 130 is arranged so as to avoid the control board 150. In particular, if a plurality of capacitors 130 are arranged so as to be arranged on the outer side side substantially symmetrical to the control board 150 connected to the flexible circuit board 160, it is easy to arrange the capacitor 130 having a large volume. Here, in the example shown in FIG. 4, two capacitors 130 are arranged as described above in order to secure the electric capacity required for the radiography apparatus 100-1. In this case, the recess 1831 shown in FIG. 2 is within 20 mm to 100 mm from the side surface 182 of the housing 180 when viewed from the Z direction, which is the incident direction of the radiation R, considering that it is gripped by a human hand. Is desirable. However, since the main body 131 of the capacitor 130 is the thickest, when the main body 131 of the capacitor 130 and the recess 1831 are overlapped when viewed from the Z direction, which is the incident direction of the radiation R, the recess 1831 is formed deeply. Becomes difficult. On the other hand, if the recess 1831 is formed in the vicinity of the side surface 182 of the housing 180 so as not to overlap with the capacitor 130, the operator needs to bend a joint such as a finger to grip it, which is generally difficult to grip. , May impair portability. Also, when viewed in FIG. Since the capacitor 130 is arranged so as to be centered, it is necessary to reduce the size of the control board 150 and the capacitor 130.

In the present embodiment, in order to cope with such a problem, as shown in FIG. 2, at least a part of the recess 1831 is viewed from a direction (X direction) orthogonal to the incident direction of the radiation R. It is formed so as to overlap the main body 131 of the capacitor 130, and at least a part of the sealing portion 132 of the capacitor 130 is between the recess 1831 and the radiation detection panel 110 in the incident direction (Z direction) of the radiation R. (Arranged so as to overlap the recess 1831 when viewed from the incident direction (Z direction) of the radiation R). Here, as can be seen from the capacitors 130 shown in FIGS. 2 and 3, since the sealing portion 132 is thinner than the main body portion 131, a deep recess 1831 can be formed. In this case, as shown in FIG. 2, since the recess 1831 is arranged between the main body 131 and the terminal 133, the recess 1831 can be provided at a position that does not impair portability.

As described above, in the radiographing apparatus 100-1 according to the first embodiment, at least a part of the recess 1831 is viewed from a direction (X direction) orthogonal to the incident direction (Z direction) of the radiation R. Occasionally, it is formed so as to overlap the main body 131 of the capacitor 130. Further, at least a part of the sealing portion 132 of the capacitor 130 has a recess 1831 (more specifically, the recessed portion of the recess 1831 toward the radiation detection panel 110) in the incident direction (Z direction) of the radiation R. It is arranged between the radiation detection panel 110 and the radiation detection panel 110.
According to such a configuration, the capacitor 130 that supplies sufficient power can be arranged inside the housing 180 while maintaining the improvement in the portability of the radiography apparatus 100-1.

(Second embodiment)
Next, a second embodiment of the present invention will be described. In the description of the second embodiment described below, the matters common to the first embodiment described above will be omitted, and the matters different from the first embodiment described above will be described.

The perspective view showing the appearance of the radiography apparatus according to the second embodiment is the same as the perspective view showing the appearance of the radiography apparatus 100 according to the first embodiment shown in FIG. Further, the internal configuration of the radiographic apparatus 100 according to the second embodiment is basically the same as the internal configuration of the radiological imaging apparatus 100-1 according to the first embodiment shown in FIG. The shape of the recess 1831 provided in the housing 180 is different.

FIG. 5 is a diagram showing an example of the internal configuration of the radiography apparatus 100 according to the second embodiment of the present invention in the I-I cross section shown in FIG. 1 (b). In the following description, the radiography apparatus 100 according to the second embodiment shown in FIG. 5 will be described as "radiography apparatus 100-2". In FIG. 5, the same components as those shown in FIG. 2 are designated by the same reference numerals, and detailed description thereof will be omitted. Further, FIG. 5 illustrates an XYZ coordinate system corresponding to the XYZ coordinate system shown in FIG.

As shown in FIG. 5, in the radiography apparatus 100-2 according to the second embodiment, the bottom portion of the recess 1831 is inclined in the XZ plane. In the radiography apparatus 100-2 according to the second embodiment, at least a part of the recess 1831 is the incident direction (Z direction) of the radiation R as in the radiography apparatus 100-1 according to the first embodiment. ), When viewed from the direction orthogonal to (X direction), it is formed so as to overlap the main body 131 of the capacitor 130. Further, at least a part of the sealing portion 132 of the capacitor 130 is arranged between the recess 1831 and the radiation detection panel 110 in the incident direction (Z direction) of the radiation R (when viewed from the incident direction (Z direction) of the radiation R). (Arranged so as to overlap the recess 1831). This allows the formation of deep recesses 1831.
Then, according to the second embodiment, similarly to the first embodiment described above, the housing 180 is provided with the capacitor 130 that supplies sufficient power while maintaining the improvement in the portability of the radiography apparatus 100-2. Can be placed inside.

(Third Embodiment)
Next, a third embodiment of the present invention will be described. In the description of the third embodiment described below, the description of the matters common to the above-mentioned first and second embodiments is omitted, and the matters different from the above-mentioned first and second embodiments are described. Give an explanation.

The perspective view showing the appearance of the radiography apparatus according to the third embodiment is the same as the perspective view showing the appearance of the radiography apparatus 100 according to the first embodiment shown in FIG.

FIG. 6 is a diagram showing an example of the internal configuration of the radiography apparatus 100 according to the third embodiment of the present invention in the I-I cross section shown in FIG. 1 (b). Note that, in FIG. 6, only a part of the region in the I-I cross section shown in FIG. 1 (b) (the recess 1831 of the housing 180 and the peripheral region of the capacitor 130, which is about the left half shown in FIG. 2) is shown. ing. In the following description, the radiography apparatus 100 according to the third embodiment shown in FIG. 6 will be described as "radiography apparatus 100-3". In FIG. 6, the same reference numerals are given to the configurations similar to those shown in FIGS. 2 and 5, and detailed description thereof will be omitted. Further, FIG. 6 illustrates the XYZ coordinate system corresponding to the XYZ coordinate system shown in FIGS. 2 and 5.

The radiographing apparatus 100-3 according to the third embodiment has the capacitor 130 and the housing 180 mainly in the incident direction (Z direction) of the radiation R with respect to the radiographing apparatus 100-1 according to the first embodiment. A protective member 190 is further provided between the back surface and the back surface of the protective member 190. Here, it is desirable that the protective member 190 is formed of an insulating material (insulating material) such as a resin or a fiber reinforced resin. Although not shown in FIG. 6, the radiography apparatus 100-3 according to the third embodiment also includes the control board 150 and the flexible circuit board 160 shown in FIG.

In the radiography apparatus 100-3 according to the third embodiment, as in the first embodiment, at least a part of the recess 1831 is in a direction (X direction) orthogonal to the incident direction (Z direction) of the radiation R. ), It is formed so as to overlap the main body 131 of the capacitor 130. Further, in the radiography apparatus 100-3 according to the third embodiment, as in the first embodiment, at least a part of the sealing portion 132 of the capacitor 130 is recessed in the incident direction (Z direction) of the radiation R. It is arranged between the 1831 and the radiation detection panel 110 (arranged so as to overlap the recess 1831 when viewed from the incident direction (Z direction) of the radiation R).

Here, when the radiography apparatus 100-3 is dropped or an external force is applied, the housing 180 is deformed, and the distance between the terminal portion 133 of the capacitor 130 and the back surface 183 of the housing 180 is reduced, so that the terminal portion 133 It is possible that the protection will be insufficient. Therefore, in the third embodiment, as shown in FIG. 6, a protective member 190 for protecting the capacitor 130 is provided between the recessed recess 1831 and the back surface 183 of the housing 180 and the terminal portion 133. It is arranged so as to cover at least a part of 133. Further, the protective member 190 is arranged as a spacer that fills the space between the support base 120 and the housing 180 in the incident direction (Z direction) of the radiation R in a part around the terminal portion 133. At this time, the protective member 190 may have a spacer structure in which the housing 180 is supported by the support base 120 when the housing 180 is deformed. By arranging the protective member 190 as a spacer between the support base 120 and the housing 180 in this way, even when the housing 180 is deformed by an external force or the like, the terminal portion 133 of the capacitor 130 can be moved to the housing 180. It is possible to reduce the risk of touching.

Further, the protective member 190 may have a structure that not only covers the terminal portion 133 of the capacitor 130 but also covers the sealing portion 132 of the capacitor 130, the main body portion 131, and the like. Further, the housing 180 may be formed of a strong fiber reinforced resin, magnesium alloy, aluminum alloy, or the like. When the housing 180 is made of a conductive material, an insulating layer may be provided in order to stably secure insulation with the capacitor 130. Similarly, the support base 120 may also be formed of a fiber reinforced resin, a magnesium alloy, an aluminum alloy, or the like.

According to the third embodiment, similarly to the first embodiment described above, the capacitor 130 that supplies sufficient power while maintaining the improvement in the portability of the radiography apparatus 100-3 is provided inside the housing 180. Can be placed in.

(Other embodiments)
In the above-described embodiment of the present invention, the formation of the recess 1831 has been described by taking the capacitor 130 as an example, but a form in which the secondary battery having the same structure is not limited to the capacitor is also applicable to the present invention. Is. Further, as in the radiography apparatus 100-4 shown in FIG. 7, the sealing portion 132 is not arranged between the recess 1831 and the radiation detection panel 110 in the incident direction (Z direction) of the radiation R, and is a terminal. There may be a configuration in which at least a part of the portion 133 is arranged between the recess 1831 and the radiation detection panel 110.

It should be noted that the above-described embodiments of the present invention merely show examples of embodiment in carrying out the present invention, and the technical scope of the present invention should not be construed in a limited manner by these. Is. That is, the present invention can be implemented in various forms without departing from the technical idea or its main features.

100: Radiation imaging device, 110: Radiation detection panel, 120: Support base, 130: Capacitor, 131: Main body, 132: Sealing part, 133: Terminal part, 140: Connection wiring, 150: Control board, 160: Flexible circuit board, 170: shock absorber, 180: housing, 181: incident surface, 182: side surface, 183: back surface, 1831: recess, R: radiation, H: subject

Claims (7)

A radiation detection panel that detects incident radiation, and
A capacitor for supplying power to the radiation detection panel and
A housing containing the radiation detection panel and the capacitor,
Have,
The capacitor includes a main body portion formed by stacking electrodes, a sealing portion that seals the periphery of the main body portion, and a terminal portion for electrically connecting to an external component portion of the capacitor. Is composed of
The housing is formed with a recess recessed toward the capacitor.
At least a part of the recess is formed so as to overlap the main body when viewed from a direction orthogonal to the incident direction of the radiation.
A radiography apparatus characterized in that at least a part of the sealing portion or the terminal portion is arranged between the recess and the radiation detection panel in the incident direction of the radiation. When viewed from the incident direction of the radiation, at least one terminal portion is arranged outside the radiographing apparatus with respect to the recess, and the main body portion sandwiches the recess in between. The radiography apparatus according to claim 1, wherein the radiography apparatus is arranged on the side opposite to the terminal portion. The radiographing apparatus according to claim 1 or 2, wherein a protective member is further provided between the capacitor and the housing in the incident direction of the radiation. The radiographing apparatus according to claim 3, wherein the protective member is arranged between the terminal portion of the capacitor and the housing in the incident direction of the radiation. The radiography apparatus according to claim 3 or 4, wherein the protective member is made of an insulating material. Further having a support base for supporting the radiation detection panel,
Claims 3 to 5 are characterized in that the protective member is arranged as a spacer between the support base and the housing in a part around the terminal portion in the incident direction of the radiation. The radiography apparatus according to any one of the above items. It is configured to have a plurality of the capacitors arranged along a direction orthogonal to the incident direction of the radiation.
The radiographing apparatus according to any one of claims 1 to 6, wherein the recess is formed at a position overlapping the plurality of capacitors when viewed from the incident direction of the radiation.

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