JP7427441B2 - radiography equipment - Google Patents

Description

The present invention relates to a radiographic apparatus having a radiation detection panel that detects incident radiation.

2. Description of the Related Art Radiographic apparatuses that obtain radiographic images by detecting the intensity distribution of radiation transmitted through a subject, which is an object to be imaged, are widely and commonly used in industrial non-destructive testing and medical diagnosis. In such radiographic apparatuses, in order to be able to rapidly image a wide range of parts of a subject, devices have been developed with consideration given to portability and operability. For example, in order to improve the portability of radiographic apparatuses, radiographic apparatuses have been proposed in which a rechargeable battery, which is a power source for supplying electric power, is built-in or detachable. For example, Patent Document 1 describes an example in which a capacitor is configured as a power source to ensure the power necessary for a radiation imaging apparatus. Further, for example, Patent Document 2 proposes a radiographic apparatus in which a gripping recess (grip portion) recessed toward the inside is formed in the exterior casing in order to improve portability.

Japanese Patent Application Publication No. 2012-237692 JP2017-67564A

However, for example, in the capacitor described in Patent Document 1, in order to supply sufficient power, a corresponding volume of the capacitor is required, and the capacitor occupies a limited volume inside the radiation imaging apparatus. On the other hand, if a grip section that is recessed toward the inside is provided, as in the case of the radiographic apparatus described in Patent Document 2, for example, in order to improve portability, the internal volume of the radiographic apparatus is reduced. It turns out. That is, in conventional radiation imaging apparatuses, it has been a problem to be able to arrange a capacitor inside that supplies sufficient power while maintaining improved portability.

The present invention has been made in view of these problems, and aims to provide a radiation imaging apparatus that can house a capacitor that supplies sufficient power while maintaining improved portability. purpose.

The radiation imaging 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 containing the radiation detection panel and the capacitor, a casing having an incident surface that is a side on which radiation is incident on the radiation detection panel and a back surface located on the opposite side to the incident surface, and the capacitor is a main body formed by laminating electrodes. and a sealing part that seals the periphery of the main body part, and is arranged closer to the back surface than the radiation detection panel, and the back surface includes a sealing part that seals the periphery of the main body part. A gripping portion that is recessed toward the radiation detection panel side is formed to grip the radiation detection panel, and an inner surface of at least a portion of the gripping portion is closer to the radiation detection panel than a portion of the main body portion. It is close to the panel and faces the sealing part with a space therebetween.

According to the present invention, a capacitor that supplies sufficient power can be placed inside the radiation imaging apparatus while maintaining improved portability.

1 is an external perspective view of a radiation imaging apparatus according to a first embodiment of the present invention. FIG. 1B is a diagram showing an example of the internal configuration of the radiographic apparatus according to the first embodiment of the present invention, taken along the line II cross section shown in FIG. 1(b). 3 is a diagram illustrating a first embodiment of the present invention and illustrating an example of a schematic configuration of a capacitor in FIG. 2. FIG. FIG. 3 is a diagram showing an example of the internal configuration of the radiation imaging apparatus according to the first embodiment of the present invention shown in FIG. 2 when viewed from the back side of the housing. FIG. 2 is a diagram showing an example of the internal configuration of the radiographic apparatus according to the second embodiment of the present invention, taken along the II cross section shown in FIG. 1(b). 1(b) is a diagram showing an example of the internal configuration of the radiographic apparatus according to the third embodiment of the present invention, taken along the line II cross section shown in FIG. 1(b). FIG. FIG. 2 is a diagram showing an example of the internal configuration of a radiation imaging apparatus according to another embodiment of the present invention, taken along the II cross section shown in FIG. 1(b).

Hereinafter, modes for carrying out the present invention (embodiments) will be described with reference to the drawings. However, the dimensions and structural details shown in each embodiment of the present invention described below are not limited to those described in the specification and drawings. Furthermore, in this 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, a first embodiment of the present invention will be described.

FIG. 1 is an external perspective view of a radiation imaging apparatus 100 according to a first embodiment of the present invention. Specifically, FIG. 1A is an external perspective view of the exterior casing of the radiation imaging apparatus 100, viewed from the side of the entrance surface 181 through which radiation enters. Further, FIG. 1(b) is an external perspective view of the exterior casing of the radiographic apparatus 100, as viewed from the side of the back surface 183 located on the opposite side to the entrance surface 181 shown in FIG. 1(a). Further, FIGS. 1A and 1B also illustrate a side surface 182 that connects the entrance surface 181 and the back surface 183. Further, as shown in FIG. 1(b), a recess 1831 is formed in the back surface 183, which is recessed toward the inside of the radiographic apparatus 100 in order to improve the portability of the radiographic apparatus 100.

FIG. 2 is a diagram showing an example of the internal configuration of the radiographic apparatus 100 according to the first embodiment of the present invention, taken along the II cross section shown in FIG. 1(b). In the following description, the radiographic apparatus 100 according to the first embodiment shown in FIG. 2 will be referred to as a "radiographic apparatus 100-1." In addition, in FIG. 2, the radiation incident direction in which the radiation R shown by the dotted arrow is incident is taken as the Z direction, and the directions orthogonal to the Z direction and mutually orthogonal directions are taken as the X and Y directions. is illustrated.

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

The radiation detection panel 110 is a component that detects the radiation R (including the radiation R that has passed through the subject H) emitted by a radiation generator (not shown) and incident thereon. Specifically, the radiation detection panel 110 converts the incident radiation R into a radiation image signal, which is an electrical signal, according to its intensity. The radiation detection panel 110 includes, for example, a sensor substrate on which a plurality of photoelectric conversion elements (sensors) are arranged, a phosphor layer (scintillator layer) arranged on the sensor substrate, a phosphor protective film, etc. This 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 converts the visible light into a radiation image signal which is an electrical signal. Further, the phosphor protective film is made of a material with low moisture permeability and is used to protect the phosphor. This radiation detection panel 110 is connected to a flexible circuit board 160. In the present embodiment, the radiation detection panel 110 is a so-called direct conversion type radiation detection panel that includes a conversion element made of a-Se or the like and a conversion element section in which electric elements such as TFTs are arranged two-dimensionally. But that's fine. Further, the material of the sensor substrate of the radiation detection panel 110 may be glass or the like, but highly flexible resin or the like may also be used, and the material is not limited to these.

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

The capacitor 130 is a power supply device for supplying power necessary for operation to the radiation detection panel 110, the control board 150, the flexible circuit board 160, etc., 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 using FIG. 3.
FIG. 3 illustrates the first embodiment of the present invention and is a diagram illustrating an example of a schematic configuration of the capacitor 130 in FIG. 2. In FIG. Specifically, FIG. 3(a) is a diagram showing an example of the external configuration of the capacitor 130 shown in FIG. 2, and FIG. 2 is a diagram illustrating an example of a schematic configuration of a capacitor 130 of No. 2. FIG. Here, in FIG. 3, the same components as those shown in FIG. 2 are designated by the same reference numerals.

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

Generally, when the capacity of a secondary battery increases, an operator can take more pictures with a single charge. However, in order to improve the capacitance of the capacitor 130, the volume of the capacitor 130 must also be increased. In addition to the radiation detection panel 110 and the capacitor 130, which is a secondary battery, it is necessary to arrange other structures such as a control board 150 inside the casing 180 of the radiation imaging apparatus 100-1. In addition, the radiographic apparatus 100-1 is likely to be radiographed while subject H such as a patient is applying a load, so it needs to have sufficient strength. Therefore, ribs, bosses, etc. are generally formed on the support base 120 and the back surface 183 of the housing 180, which are structural members, in order to improve the strength of the radiographic apparatus 100-1. It is necessary to arrange structural materials and electrical components in a limited volume inside the body 180.

As described above, although the volume of the internal space of the housing 180 of the radiation imaging apparatus 100-1 is limited, the volume of the capacitor 130 is also required to supply sufficient power, and the capacitor 130 is Due to the presence of the portion 132, the terminal portion 133, etc., 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 radiographic apparatus 100-1, the limited internal volume of the housing 180 will be further reduced. , it is necessary to use the internal space of the housing 180 more efficiently. Therefore, in this embodiment, as shown in FIG. 2, at least a part of the recess 1831 is located in 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. Furthermore, at least a portion of the sealing portion 132 of the capacitor 130 is formed to overlap with the recess 1831 (more specifically, the radiation detection panel 110 in the recess 1831) in the direction of incidence of the radiation R (Z direction). A capacitor 130 is placed between the radiation detection panel 110 and the most recessed part of the housing 180 to maintain improved portability of the radiographic apparatus 100-1 and supply sufficient power This allows for efficient placement in the limited internal space.

Further, since the terminal portion 133 of the capacitor 130 is connected to a connection wiring 140 such as a lead wire using screws, solder, or the like, a space is required. In this embodiment, at least one terminal portion 133 of the capacitor 130 (the terminal portion 133 located at the left end in FIG. 2) is closer to the radiation imaging apparatus than the recess 1831 when viewed from the incident direction of the radiation R (Z direction). It is placed outside 100-1. Furthermore, when viewed from the incident direction (Z direction) of the radiation R, the main body portion 131 of the capacitor 130 is connected to the at least one terminal portion 133 (the terminal portion 133 located at the left end in FIG. 2) with the recessed portion 1831 in between. is placed on the opposite side. With this arrangement, when an external force (impact) is applied to the radiographic 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 the housing 180 is located at a location where the housing 180 is less likely to deform. Therefore, the terminal portion 133 has a structure that can be easily protected against external force (impact).

Next, the description will move on to other components shown in FIG. 2.
The connection wiring 140 is a wiring for electrically connecting between the capacitor 130 (more specifically, the terminal portion 133 of the capacitor 130) and the control board 150.

The control board 150 is, for example, an electric board for controlling the operation of the radiation detection panel 110, an electric board for reading out a radiation image signal that is an electric signal converted by the radiation detection panel 110, and an electric board for reading out the read radiation image signal. It includes an electrical board that processes (eg, generates image data of a radiographic image). The radiation image signal (image data of a radiation image) obtained by this control board 150 is transferred to the outside of the radiation imaging apparatus 100-1, displayed on a monitor, etc., and used for diagnosis.

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

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

As explained using FIG. 1, the casing 180 has an entrance surface 181, a side surface 182, and a back surface 183. This 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. Furthermore, a recessed portion 1831 is formed on the back surface 183 of the housing 180 and is recessed toward the capacitor 130 . At this time, if the recess 1831 is deeply recessed toward the radiation detection panel 110, the operator will be able to handle it more stably, and the rigidity of the housing 180 will be improved. The internal volume of the imaging device 100-1 will be reduced.

FIG. 4 is a diagram showing an example of the internal configuration of the radiation imaging apparatus 100-1 according to the first embodiment of the present invention shown in FIG. 2 when viewed from the rear surface 183 of the housing 180. In FIG. 4, the same components as those shown in FIGS. 2 and 3 are denoted by the same reference numerals, and detailed explanation thereof will be omitted. Further, FIG. 4 illustrates an XYZ coordinate system corresponding to the XYZ coordinate system shown in FIG. 2.

In the example shown in FIG. 4, the radiographic apparatus 100-1 includes 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, two capacitors 130, a first capacitor 130-1 and a second capacitor 130-2, as the plurality of capacitors 130, are Sometimes they are arranged almost parallel. In the case of the example shown in FIG. 4, as can be seen from FIG. 2 and FIG. This means that it is formed at a position overlapping with the first and second capacitors 130-2. At this time, the recess 1831 is preferably formed to overlap the two capacitors 130 shown in FIG. 4 and to be long in the direction in which they are arranged. In the example shown in FIG. 1(b), some of the recesses 1831 are arranged long along the outer shape of the radiographic apparatus 100 in this way. Thereby, by forming the recessed portion 1831 in a large size, the space for the operator to grasp can be increased, leading to improved handling. Note that the recesses 1831 are not limited to the arrangement shown in FIG. Good too.

Further, in FIG. 4, 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, as in FIG.

Each of the plurality of capacitors 130 is arranged so as to avoid the control board 150. In particular, if the plurality of capacitors 130 are arranged along the outer side that is approximately symmetrical to the control board 150 connected to the flexible circuit board 160, it is easy to arrange the capacitors 130 with a large volume. Here, in the example shown in FIG. 4, two capacitors 130 are arranged as described above in order to ensure the electrical capacity necessary for the radiation imaging apparatus 100-1. In this case, considering that the recess 1831 shown in FIG. 2 is to be held by a human hand, it should be 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 is desirable. However, since the main body 131 of the capacitor 130 is the thickest, if the main body 131 of the capacitor 130 and the recess 1831 overlap when viewed from the Z direction, which is the incident direction of the radiation R, the recess 1831 must be formed deeply. becomes difficult. On the other hand, if the recess 1831 is formed near the side surface 182 of the casing 180 so as not to overlap the capacitor 130, the operator will have to bend the joints of their fingers or the like to grasp it, which will generally make it difficult to grip. , portability may be impaired. Also, when viewed in Figure 4. Since the capacitor 130 is arranged closer to the center, it is necessary to downsize the control board 150 and the capacitor 130.

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

As described above, in the radiation imaging apparatus 100-1 according to the first embodiment, at least a portion of the recess 1831 is located in the direction (X direction) perpendicular to the incident direction (Z direction) of the radiation R. At times, it is formed so as to overlap the main body portion 131 of the capacitor 130. Furthermore, at least a portion of the sealing portion 132 of the capacitor 130 is located in the recess 1831 (more specifically, the most recessed portion of the recess 1831 toward the radiation detection panel 110) in the direction of incidence of the radiation R (Z direction). It is arranged between the radiation detection panel 110 and the radiation detection panel 110.
According to this configuration, the capacitor 130 that supplies sufficient power can be placed inside the casing 180 while maintaining the improved portability of the radiographic apparatus 100-1.

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

The perspective view showing the external appearance of the radiographic apparatus according to the second embodiment is similar to the perspective view showing the external appearance of the radiographic apparatus 100 according to the first embodiment shown in FIG. Furthermore, the internal configuration of the radiographic apparatus 100 according to the second embodiment is basically the same as the internal configuration of the radiographic 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 radiation imaging apparatus 100 according to the second embodiment of the present invention, taken along the II cross section shown in FIG. 1(b). In the following description, the radiographic apparatus 100 according to the second embodiment shown in FIG. 5 will be referred to as a "radiographic apparatus 100-2." In FIG. 5, components similar to 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 illustrated in FIG. 2.

As shown in FIG. 5, in the radiographic apparatus 100-2 according to the second embodiment, the bottom of the recess 1831 is inclined in the XZ plane. In the radiographic apparatus 100-2 according to the second embodiment, at least a part of the recess 1831 is arranged in the direction of incidence of the radiation R (Z direction), similarly to the radiographic apparatus 100-1 according to the first embodiment. ) is formed so as to overlap the main body portion 131 of the capacitor 130 when viewed from the direction (X direction) perpendicular to the direction (X direction). Furthermore, at least a portion of the sealing portion 132 of the capacitor 130 is disposed 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). 1831). This makes it possible to form a deep recess 1831.
According to the second embodiment, similarly to the first embodiment described above, the capacitor 130 that supplies sufficient power is housed in the housing 180 while maintaining the improved portability of the radiation imaging apparatus 100-2. can be placed inside.

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

The perspective view showing the external appearance of the radiographic apparatus according to the third embodiment is similar to the perspective view showing the external appearance of the radiographic apparatus 100 according to the first embodiment shown in FIG.

FIG. 6 is a diagram showing an example of the internal configuration of the radiation imaging apparatus 100 according to the third embodiment of the present invention, taken along the II cross section shown in FIG. 1(b). Note that in FIG. 6, only a part of the area in the II cross section shown in FIG. ing. In the following description, the radiographic apparatus 100 according to the third embodiment shown in FIG. 6 will be referred to as a "radiographic apparatus 100-3." In FIG. 6, the same components as those shown in FIGS. 2 and 5 are denoted by the same reference numerals, and detailed explanation thereof will be omitted. Further, FIG. 6 illustrates an XYZ coordinate system corresponding to the XYZ coordinate system illustrated in FIGS. 2 and 5.

The radiation imaging apparatus 100-3 according to the third embodiment is different from the radiation imaging apparatus 100-1 according to the first embodiment in that the radiation imaging apparatus 100-3 mainly has a capacitor 130 and a housing 180 in the incident direction (Z direction) of the radiation R. A protective member 190 is further provided between the rear surface and the rear surface. Here, the protection member 190 is desirably made of an insulating material (insulating material) such as resin or fiber-reinforced resin. Although not shown in FIG. 6, the radiographic apparatus 100-3 according to the third embodiment is also configured to include the control board 150 and flexible circuit board 160 shown in FIG. 2.

Similarly to the first embodiment, in the radiation imaging apparatus 100-3 according to the third embodiment, at least a portion of the recess 1831 is arranged in a direction (X direction) orthogonal to the incident direction (Z direction) of the radiation R. ) is formed so as to overlap the main body portion 131 of the capacitor 130. Furthermore, in the radiation imaging apparatus 100-3 according to the third embodiment, at least a portion of the sealing portion 132 of the capacitor 130 is formed in a recessed portion in the incident direction (Z direction) of the radiation R, similarly to the first embodiment. 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 radiographic 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 becomes smaller, and the distance between the terminal portion 133 and the rear surface 183 of the housing 180 becomes smaller. There is also the possibility that protection may not be sufficient. Therefore, in the third embodiment, as shown in FIG. 133 is arranged so as to cover at least a portion of it. Further, the protection member 190 is arranged as a spacer in a part of the periphery of the terminal portion 133 so as to fill the gap between the support base 120 and the housing 180 in the direction of incidence of the radiation R (Z direction). At this time, the protection member 190 may have a spacer structure that is supported by the support base 120 when the housing 180 is deformed. In this way, by arranging the protective member 190 as a spacer between the support base 120 and the casing 180, even when the casing 180 is deformed due to an external force, the terminal portion 133 of the capacitor 130 is protected from the casing 180. It is possible to reduce the risk of coming into contact with

Further, the protective member 190 may have a structure in which it covers not only the terminal portion 133 of the capacitor 130 but also the sealing portion 132, the main body portion 131, etc. of the capacitor 130. Further, the housing 180 is preferably formed from strong fiber-reinforced resin, magnesium alloy, aluminum alloy, or the like. If the housing 180 is made of a conductive material, an insulating layer may be provided to ensure stable insulation from the capacitor 130. Further, the support base 120 may be similarly formed from fiber-reinforced resin, magnesium alloy, aluminum alloy, or the like.

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

(Other embodiments)
In the embodiment of the present invention described above, the formation of the recess 1831 has been described using the capacitor 130 as an example, but the present invention is also applicable to forms other than the capacitor as long as the secondary battery has a similar structure. It is. Furthermore, as in the radiation imaging apparatus 100-4 shown in FIG. A configuration is also possible in which at least a portion of the portion 133 is disposed between the recess 1831 and the radiation detection panel 110.

The embodiments of the present invention described above are merely examples of implementation of the present invention, and the technical scope of the present invention should not be construed as limited by these. It is. That is, the present invention can be implemented in various forms without departing from its technical idea or main features.

100: Radiographic apparatus, 110: Radiation detection panel, 120: Support base, 130: Capacitor, 131: Main body, 132: Sealing section, 133: Terminal section, 140: Connection wiring, 150: Control board, 160: Flexible circuit board, 170: Buffer member, 180: Housing, 181: Incident surface, 182: Side surface, 183: Back surface, 1831: Recessed portion, R: Radiation, H: Subject

Claims (10)

a radiation detection panel that detects incident radiation;
a capacitor for supplying power to the radiation detection panel;
A casing containing the radiation detection panel and the capacitor, the casing having an entrance surface that is a side on which radiation is incident on the radiation detection panel, and a back surface located on the opposite side to the entrance surface;
has
The capacitor includes a main body formed by stacking electrodes, and a sealing part that seals the periphery of the main body, and the capacitor is located closer to the back surface than the radiation detection panel. It is located in
A gripping portion recessed toward the radiation detection panel side is formed on the back surface for gripping the housing, and the gripping portion is recessed toward the radiation detection panel.
A radiation imaging apparatus characterized in that an inner surface of at least a portion of the grip portion is closer to the radiation detection panel than a portion of the main body portion, and faces the sealing portion with an interval therebetween. The radiation imaging apparatus according to claim 1, further comprising a protection member between the capacitor and the back surface in the incident direction of the radiation. The radiation imaging apparatus according to claim 2 , wherein the protection member is made of an insulating material. The capacitor further includes a terminal portion,
The radiation imaging apparatus according to claim 2 or 3 , wherein the protection member is disposed between the terminal portion and the back surface . further comprising a support base that supports the radiation detection panel,
The radiation imaging apparatus according to any one of claims 2 to 4 , wherein the protection member is arranged as a spacer between the support base and the back surface . The capacitor further includes a terminal portion,
The radiographic apparatus according to any one of claims 1 to 5 , wherein the terminal part and the main body part are arranged on opposite sides of each other with the grip part in between. further comprising a further capacitor different from the capacitor such that a plurality of capacitors are lined up along a direction perpendicular to the direction of incidence of the radiation;
The radiographic apparatus according to any one of claims 1 to 6 , wherein an inner surface of at least a portion of the grip portion is closer to the radiation detection panel than a portion of the further capacitor. The radiation imaging apparatus according to any one of claims 1 to 7 , wherein the gripping portion is at a distance of 20 mm or more and 100 mm or less from a predetermined side surface located on the outer periphery of the back surface . The radiographic apparatus according to any one of claims 1 to 8 , wherein the back surface has a plurality of gripping parts including at least the gripping part. The radiation imaging apparatus according to any one of claims 1 to 9 , wherein the grip portion is formed in a shape that goes around the outer periphery of the back surface .

Images