JP2010127745A - Radiographic image detecting device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To prevent damages to an electric substrate etc. and to execute appropriate operations of the detection of X-rays, by suppressing the deformations of a base to which a scintillator, the electric substrate, etc. are attached, without increasing the size of a radiological image detecting apparatus. <P>SOLUTION: A detection panel 21 is attached to one side of the base 24, while a circuit board 23 and a charging battery 25 are attached to the other side. In a state where the base 24 is built in a housing 3, the side of the charging battery 25 opposite to the side attached to the base 24 makes contact with an inner wall α of the housing 3. Since a structure where the charging battery 25 is for supporting the base 24 from below, deformations of the detecting panel 21 and the circuit board 23 attached to the base 24 can be suppressed, even if a load is applied to the housing 3. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a radiation image detection apparatus.

  In recent years, a digital radiographic image detection apparatus has been used as a method of obtaining a radiographic image by irradiating a subject with radiation and detecting the radiation transmitted through the subject. As such a radiation image detection apparatus, there is a so-called FPD (Flat Panel Detector).

  As an example of FPD, a plurality of detection elements are two-dimensionally arranged on a substrate, and radiation that has passed through the subject is irradiated to a phosphor (scintillator), and visible light that is emitted according to the amount of irradiated radiation is detected. There is an apparatus that obtains a radiation image by converting charges into photoelectric conversion elements and accumulating them in photoelectric conversion elements and reading out the charges accumulated in the photoelectric conversion elements (see Patent Document 1). Such an FPD has immediacy that a radiographic image can be obtained immediately after imaging.

  FIG. 12 is a schematic diagram of a conventional system using a radiological image detection apparatus that is an FPD.

  The radiological image detection apparatus A includes an X-ray detection unit B, irradiates the subject P with the X-rays emitted from the X-ray generation unit C, and the X-rays transmitted through the subject P are photoelectrically arranged in a two-dimensional lattice. It is detected by an X-ray detector B having a conversion element. The image signal output from the photoelectric conversion element is subjected to digital image processing in the image processing unit D, and an X-ray image of the subject P is displayed on the monitor E.

  FIG. 13 is a longitudinal sectional view of a conventional radiographic image detection apparatus A.

  A metal base A3 is attached to the housing A1 via a spacer A2, and an X-ray detector B is provided on the base A3. The X-ray detector B does not chemically react with the semiconductor element, withstands the temperature of the semiconductor process, and requires dimensional stability, etc., so that the substrate B1 formed of a glass plate is formed in a two-dimensional array by the semiconductor process. The photoelectric conversion element B2 and the fluorescent plate B3 obtained by applying a phosphor made of a metal compound to a resin plate are integrally laminated.

On the lower surface of the base A3, a circuit board A4 on which electronic parts for processing an electric signal subjected to photoelectric conversion are mounted is fixed via a protrusion A5. The circuit board A4 and the photoelectric conversion element B2 are connected by a flexible circuit board A6.
JP 2001-346788 A

  By the way, since the subject P lies down or sits on the radiographic image detection apparatus A during X-ray imaging, the radiographic image detection apparatus A is in the direction in which the X-ray detection unit B is installed as shown in FIG. A constant load F is applied. As a result of the load F being applied, the casing A is deformed as indicated by a broken line, and if the X-ray detection unit B and the circuit board A4 are similarly deformed, the circuit board A4 is damaged, and the X-ray is appropriately applied. May not be possible.

  Therefore, it is necessary to make the radiation image detection apparatus A have a strong structure. For example, as in the technique described in Patent Document 1, the base A3 on which the X-ray detection unit B and the circuit board A4 are installed has a certain thickness. It is made of a certain metal so that the base A3 is not deformed. However, if the base A3 is made of metal, the radiation image detection device A becomes heavy, and if the radiation image detection device A is portable, it is difficult to carry. Further, if the thickness of the base A3 is increased in order to ensure the rigidity of the base A3, the thickness of the radiation image detection apparatus A in the X-ray incident direction increases, and the radiological image detection apparatus A becomes larger and thinner. It is not preferable.

  Accordingly, an object of the present invention is to prevent the breakage of the electric substrate and the like by suppressing the deformation of the base on which the scintillator and the electric substrate are installed without increasing the size of the radiation image detection apparatus. A radiological image detection apparatus capable of executing a detection operation is provided.

In order to achieve the above object, a radiological image detection apparatus according to the present invention comprises:
A radiological image detection apparatus for detecting radiation emitted toward a subject,
A detector panel having a scintillator that converts incident radiation into light, and a detector that receives the light converted by the scintillator and converts it into an electrical signal;
An electric board for processing the electric signal converted by the detection unit;
A power supply for supplying power to the detector panel and the electrical board;
A base on which the detector panel is mounted on one surface and the electric board and the power supply unit are mounted on the other surface;
A housing containing at least the base,
In a state where the base is built in the casing, a surface of the power supply unit opposite to the mounting surface with respect to the base is held on an inner wall of the casing. .

  According to the radiological image detection apparatus of the present invention, the deformation of the base on which the scintillator, the electric board, etc. are installed is suppressed without increasing the size of the radiographic image detection apparatus, and the electric board etc. is prevented from being damaged. Appropriate line detection operations can be performed.

  [Outline of Cassette Type Detector] FIG. 1 is a perspective view of a cassette type detector in the present embodiment.

  A cassette type detector 1 as a radiation image detecting apparatus is a cassette type flat panel detector (hereinafter referred to as “FPD”). The cassette-type detector 1 includes a detector unit 2 (see FIG. 3 and the like) that detects irradiated radiation and acquires it as digital image data, and a housing (housing) 3 that houses the detector unit 2 therein. I have.

  In this embodiment, the housing 3 is formed so that the thickness in the radiation incident direction is 15 mm. The thickness of the housing 3 in the radiation incident direction is preferably 16 mm or less, and a size (15 mm + 1 mm and 15 mm-2 mm) conforming to the JIS standard (JIS Z 4905) for a conventional screen / film cassette. (The international standard corresponding to JIS Z 4905 is IEC 60406).

  FIG. 2 is an exploded perspective view of the housing 3 in the present embodiment.

  As shown in FIG. 2, the housing 3 includes a hollow housing body 31 having openings 311 and 312 at both ends, a first lid member 32 that covers the openings 311 and 312 of the housing body 31, and a first cover member 32. 2 lid members 33.

  For example, the housing main body 31 is formed by winding a carbon fiber on a core material (mold) to obtain a desired thickness (for example, 1 mm to 2 mm), and then adjusting the shape, and thermosetting the wound carbon fiber. It is formed by pouring the resin, molding it by baking at high temperature and pressure, and then removing the core material. In addition, a rectangular plate-like member having a desired thickness (for example, 1 mm to 2 mm) and matching the developed length of the housing body 31 of a predetermined size is formed in advance, and this plate-like member is formed along the core material (mold). It is good also as a rectangular tube shape by bend | folding and couple | bonding end surfaces with an adhesive agent etc.

  The first lid member 32 and the second lid member 33 include lid body portions 321 and 331 and insertion portions 322 and 332, and are formed of a nonconductive material such as a nonconductive plastic. ing.

  Engagement pieces 324 and 334 that engage the first lid member 32 and the second lid member 33 and the housing main body 31 are provided on the side surfaces of the insertion portions 322 and 332 with respect to the openings 311 and 312. It extends toward the insertion direction. Engagement projections 325 and 335 are provided on the outer surfaces of the engagement pieces 324 and 334, respectively. When the first lid member 32 and the second lid member 33 are inserted into the housing main body portion 31, the engagement convex portions 325 and 335 engage with the engagement concave portions 315 and 316 installed in the housing main body portion 31. .

  An antenna device 9 for transmitting and receiving information wirelessly between the cassette type detector 1 and an external device is embedded in one side surface of the lid main body portion 321 of the first lid member 32. 9 includes a pair of flat radiation plates 91 and 92 made of metal, and a power feeding unit 93 that feeds power to the pair of radiation plates 91 and 92.

  Since the antenna device 9 is provided at a position close to a conductive member made of a conductive material such as metal or carbon, the reception sensitivity and the reception gain are lowered. Therefore, the housing main body formed of a conductive material such as carbon is used. 31 and various electronic parts 22 made of metal or the like (refer to FIG. 3 or the like) are preferably provided as far as possible.

  Further, on one surface of the lid main body portion 321 and the same surface as the surface on which the antenna device 9 is formed, the rechargeable battery 25 as a power supply unit provided inside the housing 3 (see FIG. 3 and the like). A charging terminal 45 connected to an external power source or the like when charging the battery and a power switch 46 for switching ON / OFF of the power source of the cassette type detector 1 are provided. Furthermore, the corner 47 formed by the surface on which the antenna device 9 is formed and the surface on the radiation incident side is composed of, for example, an LED or the like, and an indicator 47 that displays the charging status of the rechargeable battery 25 and various operating statuses. Is provided.

  [Internal Structure of Cassette Type Detector] Next, the internal structure of the cassette type detector 1 will be described. 3 is a plan view of the state in which the detector unit 2 is housed in the housing 3 as viewed from the upper side (radiation incident side during imaging), FIG. 4 is a cross-sectional view taken along line AA in FIG. 3, and FIG. FIG. 5 is a cross-sectional view taken along line BB in FIG. 3. FIG. 3 schematically shows the arrangement of each member in the cassette type detector 1 when the upper surface of the housing 3, the buffer member 26, the detection panel 21, and the base 24 are removed for convenience of explanation. Yes.

As shown in FIG. 4, the detector unit 2 includes a detection panel 21, a circuit board (electric board) 23 on which various electronic components 22 are mounted, and the like. In the present embodiment, the detection panel 21 and the circuit board 23 are attached to a base 24 made of resin. Although not shown in FIG. 4, a part of the detection panel 21 and the predetermined circuit board 23 are connected by a flexible harness.
The base 24 is flexible and is made of a thin resin. The thickness is about 1 mm, and the material is, for example, a resin in which polycarbonate and ABS are mixed. In this way, the base 24 is formed of a flexible resin, and by reducing the weight, it is possible to improve the ability to set the affected area at the time of photographing and the portability when the cassette type detector 1 is moved.

  The detection panel 21 is a scintillator layer 211 formed on one surface as a scintillator that converts incident radiation into light, and is laminated on the lower side of the scintillator layer 211 and converted by the scintillator layer 211. A signal detection unit 151 (see FIG. 7), which is a detection unit that detects light and converts it into an electrical signal, includes a second glass substrate 213 formed on one surface, and these are laminated. It has a laminated structure.

  As shown in FIG. 3, in the present embodiment, the circuit board 23 on which the electronic component 22 is mounted is divided into four parts, and each circuit board 23 is detected in a state where the base 24 is built in the housing 3. The panel 21 is arranged near each corner. The electronic component 22 is disposed on the circuit board 23 along the outer periphery of the detection panel 21. The electronic component 22 is preferably disposed at a position as close to each corner of the detection panel 21 as possible. By disposing the electronic component 22 on the circuit board 23 in this way, when the detector unit 2 is housed in the housing 3, the electronic component 22 is subjected to external forces in the vicinity of the corner of the housing 3 and the peripheral portion of the housing main body 31. Are arranged along regions that are difficult to deform. This is because external force such as weight at the time of imaging of the patient is affected by external force damage to the internal circuit board 23 and the electronic component 22 due to the central portion of the housing 3 as viewed from the X-ray incident direction is most affected by the external force. Is to avoid. In addition, the number, arrangement | positioning, etc. of the circuit board 23 and the electronic component 22 are not limited to what was illustrated here.

  In the present embodiment, as the electronic component 22 arranged on the circuit board 23, for example, a CPU (Central Processing Unit), a ROM (Read Only Memory), and a ROM constituting a control unit 28 (see FIG. 10) that controls each unit. There are a storage unit (not shown) including a RAM (Random Access Memory), a scanning drive circuit 16 (see FIG. 7), a signal readout circuit 17 (see FIG. 7), and the like.

  The detector unit 2 is provided with a communication unit (not shown) that transmits and receives various signals to and from an external device. For example, the communication unit transfers the image signal output from the detection panel 21 to the external device via the antenna device 9 described above, and receives the imaging start signal transmitted from the external device via the antenna device 9. It has come to be.

  A central portion on the base 24 has a plurality of driving units (for example, a scanning driving circuit 16 (see FIG. 7), a signal reading circuit 17 (see FIG. 7) described later), a communication, which constitute the cassette type detector 1. A rechargeable battery 25 is provided to supply power to a unit (not shown), a storage unit (not shown), a charge amount detection unit (not shown), an indicator 47, a detection panel 21 and the like.

  In this embodiment, an electric double layer capacitor is used as the rechargeable battery 25. However, in addition to the electric double layer capacitor, a rechargeable battery such as a lithium ion capacitor, a nickel cadmium battery, a nickel metal hydride battery, a lithium ion battery, a small sealed lead battery, or a lead storage battery can be applied.

  The rechargeable battery 25 is electrically connected to the aforementioned charging terminal 45 by being installed at a predetermined position on the base 24. For example, the cassette type detector 1 is connected to an external power source. By attaching to a charging device such as a cradle (not shown), the terminal on the charging device side and the charging terminal 45 on the housing 3 side are connected and the rechargeable battery 25 is charged. .

  As shown in FIG. 5, a flexible harness 327 made of a flexible material is provided at an end portion of the circuit board 23 connected to the various electronic components 22 and the rechargeable battery 25.

  The circuit board 23 and the like are electrically connected to the charging terminal 45, the power switch 46, the indicator 47, and the antenna device 9 as interface parts provided on the first lid member 32 by the flexible harness 327. ing.

  Between the inner wall of the housing 3 and the detection panel 21, a buffer member 26 is installed to absorb a sudden impact caused by a drop of the cassette type detector 1 or a collision with something.

  [Circuit Configuration of Detection Panel] Next, the circuit configuration of the detection panel 21 will be described. FIG. 6 is an equivalent circuit diagram of a photoelectric conversion unit for one pixel constituting the signal detection unit 151.

  As shown in FIG. 6, the configuration of the photoelectric conversion unit for one pixel is a photodiode 152 and a thin film transistor (hereinafter referred to as “TFT”) 153 that extracts electric energy accumulated in the photodiode 152 as an electric signal by switching. It consists of and. The photodiode 152 is an image sensor that generates and accumulates charges. The electrical signal taken out from the photodiode 152 is amplified by an amplifier 154 to a level that can be detected by the signal readout circuit 17.

  Specifically, when light is irradiated, a charge is generated in the photodiode 152, and when a signal reading voltage is applied to the gate G of the TFT 153, the charge is transferred from the photodiode 152 connected to the source S of the TFT 153. It flows to the drain D side of the TFT 153 and is stored in a capacitor 154 a connected in parallel to the amplifier 154. The amplifier 154 outputs an electric signal amplified in proportion to the electric charge accumulated in the capacitor 154a.

  When the amplified electrical signal is output from the amplifier 154 and the electrical signal is extracted, the switch 154b connected in parallel to the amplifier 154 and the capacitor 154a is turned on, and the charge accumulated in the capacitor 154a is released. The amplifier 154 is reset. The photodiode 152 may simply be a photodiode having a regulation capacitance, or may include an additional capacitor in parallel so as to improve the dynamic range of the photodiode 152 and the photoelectric conversion unit.

  FIG. 7 is an equivalent circuit diagram in which such photoelectric conversion units are two-dimensionally arranged. Between the pixels, the scanning lines Ll and the signal lines Lr are arranged so as to be orthogonal to each other. One end side of the photodiode 152 is connected to the source S of the TFT 153, and the drain D of the TFT 153 is connected to the signal line Lr. On the other hand, the other end side of the photodiode 152 is connected to the other end side of the adjacent photodiode 152 arranged in each row, and is connected to a bias power source 155 through a common bias line Lb.

  The bias power source 155 is connected to the control unit 28, and a voltage is applied to the photodiode 152 through the bias line Lb according to an instruction from the control unit 28. The gates G of the TFTs 153 arranged in each row are connected to a common scanning line Ll, and the scanning line Ll is connected to the control unit 28 via the scanning drive circuit 16. Similarly, the drain D of the TFT 153 arranged in each column is connected to the signal readout circuit 17 connected to the common signal line Lr and controlled by the control unit 28.

  The signal readout circuit 17 is provided with the amplifier 154 for each signal line Lr described above. At the time of signal reading, a signal reading voltage is applied to the selected scanning line Ll, whereby a voltage is applied to the gate G of each TFT 153 connected to the scanning line Ll, and each photodiode is connected via each TFT 153. The charge generated in the photodiode 152 flows from the signal line 152 to each signal line Lr. Then, each amplifier 154 amplifies the charge for each photodiode 152, and information of the photodiode 152 for one row is extracted. This operation is performed for all the scanning lines Ll by switching the scanning lines Ll, whereby information is extracted from all the photodiodes 152.

  A sample hold circuit 156 is connected to each amplifier 154. Each sample and hold circuit 156 is connected to an analog multiplexer 157 provided in the signal readout circuit 17, and the signal read out by the signal readout circuit 17 is described above from the analog multiplexer 157 via the A / D converter 158. It is output to the control unit 28.

  Note that the TFT 153 may be either an inorganic semiconductor type used in a liquid crystal display or the like, or an organic semiconductor type.

  Further, in the present embodiment, the case where the photodiode 152 as a photoelectric conversion element is used as the imaging element is illustrated, but a solid-state imaging element other than the photodiode may be used as the photoelectric conversion element.

  As described above, the X-ray image of the subject can be detected by using the cassette type detector 1 as shown in FIGS.

  [Preventing deformation of detection panel and the like] As shown in FIG. 4, the lower surface α of the cassette type detector 1 is set on the detection base during X-ray imaging, and the subject lies or sits on the upper surface β of the cassette type detector 1. Or Accordingly, a constant load F (see FIG. 4) is applied to the cassette type detector 1 due to the weight of the subject. If the detection panel 21 or the circuit board 23 is deformed as a result of the load F being applied, the electronic component 22 or the circuit board 23 may be damaged, and an appropriate X-ray detection operation may not be performed. Therefore, in the cassette type detector 1, the base 24 is supported by the rechargeable battery 25 to suppress deformation of the detection panel 21 and the like.

  As shown in FIG. 4, one surface (attachment surface) of the rechargeable battery 25 is attached in close contact with the base 24, but the other surface (surface opposite to the attachment surface) of the rechargeable battery 25 is the housing 3. The rechargeable battery 25 supports the base 24 from below. Since the rechargeable battery 25 is generally strong and the rechargeable battery 25 supports the base 24 from below, a certain load F is applied to the cassette type detector 1 due to the weight of the subject during X-ray imaging. However, the base 24 is not greatly deformed. As a result, since the detection panel 21 and the circuit board 23 attached to the base 24 are not greatly deformed, the electronic component 22 and the circuit board 23 can be prevented from being damaged, and an appropriate X-ray detection operation can be executed. .

  Further, if the base 24 is supported by the rechargeable battery 25 from below, it is not necessary to suppress the deformation of the detection panel 21 and the like by the base 24 by forming the base 24 with a metal having a certain thickness, as described above. The base 24 can be formed of a thin resin. As a result, the cassette type detector 1 is reduced in weight and is easy to carry. Moreover, since the base 24 can be made thin and the entire cassette detector 1 can be made smaller and thinner, the size of the housing 3 can be reduced to a size that conforms to the JIS standard, and the versatility of the cassette detector 1 can be reduced. Can also be secured. Furthermore, by reducing the thickness of the base 24, the degree of freedom in designing the housing 3 such as the arrangement and selection of components built in the housing 3 can be increased.

  When the base 24 is supported from below by the rechargeable battery 25, if the rechargeable battery 25 directly interferes with the inner wall 3 </ b> A of the housing 3, concentrated stress may be generated and damaged. A cushioning material may be attached to the opposite surface.

3, the rechargeable battery 25 is attached to the center of the base 24 (in the present invention, even if the middle of the rechargeable battery 25 is slightly shifted from the middle of the base 24, the rechargeable battery 25 is If it is attached to a portion corresponding to the center of the base 24, it is regarded that “the rechargeable battery 25 is attached to the central portion of the base 24”). During X-ray imaging, a large load is often applied near the center of the base 24 due to the load of the subject, and the vicinity of the center of the base 24 may be greatly deformed. Therefore, when one rechargeable battery 25 is installed, the rechargeable battery 25 is attached to the central portion of the base 24 to efficiently suppress deformation of the detection panel 21 and the base 24 with a small number of rechargeable batteries 25. I can do it.
Next, the structure of the rechargeable battery 25 will be described. The rechargeable battery 25 is formed of an electric double layer capacitor from the viewpoint of shortening the charging time. FIG. 8 is a cross-sectional view of a rechargeable battery 25 formed of an electric double layer capacitor.

  The rechargeable battery 25 is configured by overlapping basic cells 251 in multiple layers. 25A and 25B are top and bottom plates made of conductive elastic material (for example, conductive rubber), 25C is a carbon paste electrode made of activated carbon powder and electrolyte solution (for example, sulfuric acid aqueous solution), and 25D is ion-permeable. A non-conductive porous separator 25E is a side wall made of an electrically insulating elastic body (for example, rubber). The upper lid 25A and the bottom plate 25B serve as the capacitor electrodes.

  The rechargeable battery 25, which is such an electric double layer capacitor, generates oxygen from the top lid 25A and the bottom plate 25B, which are electrodes of the capacitor, by repeating the charging and discharging operations. If this oxygen stays between the top cover 25A and the bottom plate 25B, the ionic reaction in the carbon paste electrode 25C is hindered, and the time for charging the rechargeable battery 25 to a predetermined value after the discharge operation will become long.

  However, since the rechargeable battery 25 applies a load on the subject during X-ray photography and pressure is applied between the upper lid 25A and the bottom plate 25B, oxygen generated in the upper lid 25A and the bottom plate 25B is extracted toward the side wall 25E. -The ion reaction in the paste electrode 25C is not inhibited, and the time for charging the rechargeable battery 25 to a predetermined value after the discharging operation is shortened. That is, if the rechargeable battery 25 that supports the base 24 from below is formed of an electric double layer capacitor, the performance of the rechargeable battery 25 is appropriately maintained.

  An experiment was conducted to confirm how much the charging time differs depending on whether the rechargeable battery 25 is pressurized or not. The experimental results are shown in the graph shown in FIG.

  The vertical axis of the graph shown in FIG. 9 indicates the charge capacity [mAh], and the horizontal axis indicates the elapsed time [sec] since the start of charging. A solid line in FIG. 9 indicates a state of charge when the rechargeable battery 25 is pressurized, and a broken line indicates a state of charge when the rechargeable battery 25 is not pressurized.

  As shown in FIG. 9, it can be confirmed that the time from when charging is started until the predetermined charging reference value “a” is reached is shorter when pressure is applied to the rechargeable battery 25 than when pressure is not applied. It was. When a pressure of 0.8 kg is applied to the rechargeable battery 25 per unit area of 1 cm 2, until charging reaches a predetermined charging reference value a after starting charging as compared to the case without pressing. Is shortened to 250 sec (seconds). By shortening the charging time, the shooting cycle is shortened, and many shootings can be performed efficiently.

  It should be noted that when a subject's load is applied during X-ray imaging, the buffer member 26 (see FIG. 4) presses the rechargeable battery 25 via the detection panel 21, the base 24, etc. It is possible to shorten the charging time of the rechargeable battery 25 by providing the buffer member 26 so as to fill the gap. By shortening the charging time, the shooting cycle is shortened, and many shootings can be performed efficiently.

  [Other Embodiments] FIGS. 10 and 11 show another embodiment different from the present embodiment. FIG. 10 is a plan view showing another embodiment of the state in which the detector unit 2 is housed in the housing 3 as viewed from the upper side (radiation incident side at the time of imaging), and FIG. 11 shows the spacer 27 on the circuit board 23. It is sectional drawing of the installed cassette type | mold detector 1. FIG.

  First, in the embodiment shown in FIG. 10, unlike the embodiment shown in FIG. 3, two rechargeable batteries 25 are attached to the base 24 and the base 24 is supported from below by the two rechargeable batteries 25. ing. Even in the embodiment shown in FIG. 10, since the detection panel 21 and the circuit board 23 attached to the base 24 are not greatly deformed, the electronic component 22 and the circuit board 23 are prevented from being damaged, and the X-ray The appropriate detection operation can be executed. Moreover, the load applied to the housing 3 by the plurality of rechargeable batteries 25 can be dispersed, and mechanical damage to the rechargeable battery 25 due to the loads can be reduced.

  Furthermore, when installing the two rechargeable batteries 25, it is preferable to install so that the two rechargeable batteries 25 may oppose the diagonal of the base 24 as shown in FIG. When a large load is applied to the central portion of the base 24, the base 24 and the like are greatly deformed on the diagonal line of the base 24, and thus the arrangement of the detection panel 21 and the base 24 and the like is achieved by such an arrangement. Deformation can be efficiently suppressed.

  Next, in another embodiment shown in FIG. 11, a spacer 27 is attached to the circuit board 23. In the state in which the base 24 is built in the housing 3, as shown in FIG. 11, one surface (mounting surface) of the spacer 27 is attached in close contact with the circuit board 23, but the other surface of the spacer 27 ( The surface opposite to the mounting surface) is held on the inner wall 3A of the housing 3, and a spacer 27 together with the rechargeable battery 25 supports the base 24 from below. Thus, by supporting the base 24 from below with the rechargeable battery 25 and the spacer 27, even if a larger load is applied to the housing 3, the deformation of the base 24 and the detection panel 21 can be suppressed. It is also possible to reduce the mechanical damage of the rechargeable battery 25 due to the load by dispersing the load applied to. In addition, there are various design restrictions in order to reduce the thickness of the cassette type detector 1. However, since there are many places where the base 24 is supported from below, the base 24 can be freely arranged. The degree of freedom in design can be increased.

  Further, when the base 24 is supported from below by the rechargeable battery 25 and the spacer 27, if the rechargeable battery 25 or the spacer 27 directly interferes with the inner wall 3 </ b> A of the housing 3, concentrated stress may be generated and damaged. Alternatively, a cushioning material may be attached to the surface of the spacer 27 (in the spacer 27, the surface opposite to the installation surface of the spacer 27 with respect to the circuit board 23). In some cases, the base 24 may be supported by the spacer 27 only from below.

  In addition, this invention is not limited to the said embodiment, Even if there exists a change and addition in the range which does not deviate from the summary of this invention, it is contained in this invention.

  In the present embodiment, the indirect conversion type FPD in which the detection panel 21 includes the scintillator layer 211 and the signal detection unit 151 has been described as an example, but the FPD is not limited to the indirect conversion type. For example, an amorphous selenium (a-Se) layer that absorbs radiation and converts the radiation into electric charge is provided, and radiation photons are drawn into the a-Se layer at a high voltage, so that Even in a direct conversion type FPD that directly converts radiation energy into an electric charge amount (electrical signal), the configuration of the present invention in which the a-Se layer is sandwiched between two glass substrates can be applied. .

It is a perspective view which shows the cassette type detector which concerns on this embodiment. It is a disassembled perspective view of the housing in this embodiment. It is the schematic which shows the internal structure of the cassette type detector shown in FIG. It is AA sectional drawing of FIG. It is BB sectional drawing of FIG. It is an equivalent circuit block diagram for 1 pixel of the photoelectric conversion part which comprises a signal detection part. FIG. 7 is an equivalent circuit configuration diagram in which the photoelectric conversion units illustrated in FIG. 6 are two-dimensionally arranged. It is sectional drawing of the rechargeable battery formed with the electric double layer capacitor. It is a graph which shows the charge time of a rechargeable battery. It is the schematic which shows another internal structure of a cassette type | mold detector. It is sectional drawing of the cassette type detector by which the spacer was installed in the electronic component. It is the schematic of the conventional system using the radiographic image detection apparatus which is FPD. It is a longitudinal cross-sectional view of the conventional radiographic image detection apparatus.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Cassette type | mold detector 2 Detector unit 3 Housing 9 Antenna apparatus 21 Detection panel 22 Electronic component 23 Circuit board 24 Base 25 Rechargeable battery 26 Buffer member 27 Spacer 31 Housing main-body part 32 1st cover member 33 2nd cover member 45 Charging Terminal 46 Power Switch 47 Indicator 151 Signal Detection Section 211 Scintillator Layer 212 First Glass Base Material 213 Second Glass Base Material

Claims (9)

A radiological image detection apparatus for detecting radiation emitted toward a subject,
A detector panel having a scintillator that converts incident radiation into light, and a detector that receives the light converted by the scintillator and converts it into an electrical signal;
An electric board for processing the electric signal converted by the detection unit;
A power supply for supplying power to the detector panel and the electrical board;
A base on which the detector panel is mounted on one surface and the electric board and the power supply unit are mounted on the other surface;
A housing containing at least the base,
In the state where the base is built in the housing, a surface opposite to the mounting surface of the power supply unit with respect to the base is held on the inner wall of the housing. apparatus. The radiographic image detection apparatus according to claim 1, wherein the power supply unit is attached to a central portion of the base. The radiographic image detection apparatus according to claim 1, wherein a plurality of the power supply units are attached to the base. The radiographic image detection apparatus of any one of Claim 1 to 3 with which the shock absorbing material is attached to the surface on the opposite side to the attachment surface with respect to the said base of the said electric power supply part. Spacers are installed on the electric board,
5. The device according to claim 1, wherein the surface of the spacer opposite to the installation surface of the spacer with respect to the electric board is held on the inner wall of the housing in a state where the base is built in the housing. The radiological image detection apparatus of Claim 1. The radiation image detection apparatus according to claim 5, wherein a buffer material is attached to a surface of the spacer opposite to the installation surface with respect to the electric substrate. The radiographic image detection apparatus according to claim 1, wherein the power supply unit is formed of an electric double layer capacitor. The radiographic image detection apparatus according to claim 1, wherein the base is made of resin. The radiographic image detection apparatus according to any one of claims 1 to 8, wherein the electric board is arranged in the vicinity of a corner of the casing in a state where the base is built in the casing. .

Images