JP5986523B2 - Radiation imaging equipment - Google Patents

Description

  The present invention relates to a radiographic image capturing apparatus, and more particularly to a radiographic image capturing apparatus having a function of cooling an imaging stand having a built-in radiation detection panel.

  As a medical radiographic imaging apparatus, mammography for the purpose of early detection of breast cancer and the like is known. In mammography, a breast as a subject to be imaged is sandwiched between the imaging surface of the imaging table and a compression plate, and a radiographic image is captured in a state where the breast is compressed by the compression plate. The imaging table has a built-in radiation detection panel, and the radiation transmitted through the breast is detected by the radiation detection panel.

  The following Patent Documents 1 to 3 disclose a radiographic imaging apparatus (mammography) including a cooling device for a radiation detection panel (radiation detector) assembled in an imaging table. This cooling device is configured to allow air as a cooling medium to flow along the detection surface of the radiation detection panel and to uniformly cool the entire radiation detection panel.

Japanese Patent No. 5042756 Japanese Patent No. 50442757 Japanese Patent No. 5042760

  By the way, in the radiation detection panel, a charge signal as radiation image information is generated from radiation. The charge signal is converted into a voltage signal by a charge amplifier, and a radiation image is generated by performing image processing on the voltage signal. In order to suppress noise on the charge signal before signal conversion by the charge amplifier, a circuit board on which the charge amplifier is mounted is disposed in the vicinity of the radiation detection panel. However, since the charge amplifier becomes a heat generation source with its operation, there is a concern about the influence of heat on the radiation detection panel. On the other hand, in a direct conversion type FPD (Flat Panel Detector) type radiation detection panel that directly converts radiation into a charge signal, amorphous selenium is used in a radiation-to-charge signal conversion layer. The radiation detection panel itself does not serve as a heat source, but the conversion layer is damaged due to alteration at a low temperature.

  For this reason, in the radiographic imaging devices disclosed in Patent Documents 1 to 3, the radiation detection panel is cooled. However, since the heat generation source is not targeted for cooling, a sufficient cooling effect cannot be expected. .

  In view of the above facts, the present invention has an object to obtain a radiographic imaging apparatus capable of effectively suppressing or preventing damage to a radiation detection panel by enhancing the cooling effect of a signal conversion circuit board serving as a heat source. .

In order to solve the above-described problems, a radiographic imaging apparatus according to a first embodiment of the present invention is provided above a medium feeding path through which a cooling medium is fed from one end to the other end, and above the medium feeding path. A radiation detection panel for generating a charge signal from radiation, and a signal conversion circuit board disposed on both sides of a medium feed path parallel to the feed direction of the cooling medium and having a function of converting the charge signal into a voltage signal And a cooling medium diverting section that is provided in the medium feeding path, and that divides the cooling medium and guides it to the signal conversion circuit board side, and is disposed below the medium feeding path and is connected to the other end of the medium feeding path. And a medium discharge path for discharging the cooling medium fed to the medium feed path through the formed first ventilation portion .

  In the radiographic imaging apparatus according to the first embodiment, the charge signal generated from the radiation by the radiation detection panel is converted into a voltage signal in the signal conversion circuit board. Since the radiation detection panel is disposed above the medium feeding path and the signal conversion circuit boards are disposed on both sides of the medium feeding path, the distance from the radiation detection panel to the signal conversion circuit board is short. Therefore, noise is difficult to ride on the charge signal.

Here, the signal conversion circuit board is disposed on both sides of the medium feeding path in parallel with the cooling medium feeding direction, and a cooling medium branching section is provided in the medium feeding path. The cooling medium diverter divides the cooling medium and guides it to the signal conversion circuit board. For this reason, since the cooling medium flows along the signal conversion circuit board, the heat generated by the operation of the signal conversion circuit board is absorbed by the cooling medium.
In addition, in the radiographic image capturing apparatus, the medium discharge path is provided below the medium supply path via the first ventilation portion formed at the other end of the medium supply path. The cooling medium is discharged in one direction from the medium to the medium discharge path. For this reason, since the stagnation of the flow of the cooling medium is effectively suppressed, the cooling efficiency is improved.

The radiographic image capturing apparatus according to the second embodiment of the present invention is provided with a medium feeding path through which a cooling medium is fed from one end to the other end, and disposed above the medium feeding path, and generates a charge signal from the radiation. Radiation detection panel, a signal conversion circuit board disposed on both sides of the medium feeding path parallel to the feeding direction of the cooling medium and having a function of converting a charge signal into a voltage signal, and in the medium feeding path And a cooling medium diverting section that is configured by a V-shaped deflecting plate that spreads from one end side to the other end side of the medium feeding path and that diverts the cooling medium and guides it to the signal conversion circuit board side. ing.

In the radiographic imaging device according to the second embodiment, the signal conversion circuit boards are disposed on both sides of the medium feeding path in parallel with the feeding direction of the cooling medium, and the cooling medium is disposed in the medium feeding path . A diversion part is provided. The cooling medium diverter divides the cooling medium and guides it to the signal conversion circuit board. For this reason, since the cooling medium flows along the signal conversion circuit board, the heat generated by the operation of the signal conversion circuit board is absorbed by the cooling medium.
In addition, in the radiographic imaging apparatus, the cooling medium diverting portion is constituted by a polarizing plate, and this polarizing plate has a V-shape that widens from one end side to the other end side of the medium feeding path. For this reason, the cooling medium flowing in the medium feeding path is diverted by the polarizing plate, and the flow of the cooling medium is deflected toward the signal conversion circuit board side disposed on both sides of the medium feeding path.

The radiographic imaging apparatus according to the third embodiment of the present invention is the radiographic imaging apparatus according to the first embodiment , and is provided in the medium discharge path, and has a function of image processing for generating a radiographic image from a voltage signal. The image processing circuit board is provided.

  In the radiographic imaging device according to the third embodiment, since the image processing circuit board is provided in the medium discharge path, the heat generated by the operation of the image processing circuit board is absorbed by the cooling medium to be discharged. The This effectively suppresses or prevents the image processing circuit board from becoming a heat source and damaging the radiation detection panel.

  The radiographic image capturing apparatus according to the fourth embodiment of the present invention is the radiographic image capturing apparatus according to the third embodiment, wherein a part of the image processing circuit board is penetrated and the cooling medium from the first ventilation portion is discharged into the medium. A board penetration part for discharging to the road is provided.

  In the radiographic image capturing apparatus according to the fourth embodiment, since the substrate penetrating portion is provided in a part of the image processing circuit board, it is orthogonal to the cooling medium discharge direction from the first ventilation section to the medium discharge path. The cross-sectional area (cross-sectional area through which the cooling medium flows) is increased. For this reason, since the stagnation of the flow of the cooling medium is effectively suppressed, the cooling efficiency is improved. In addition, since the cooling medium flows along the image processing circuit board from the substrate penetrating portion, the image processing circuit board is cooled from its central portion, and the cooling efficiency of the image processing circuit board is improved.

  A radiographic imaging device according to a fifth exemplary embodiment of the present invention is the radiographic imaging device according to any one of the first to fourth exemplary embodiments, and releases heat from the signal conversion circuit board into the medium feeding path. It has a heat sink.

  In the radiographic image capturing apparatus according to the fifth embodiment, since the heat sink that releases heat from the signal conversion circuit board is provided in the medium feeding path, the cooling efficiency of the signal conversion circuit board is improved.

The radiographic image capturing device according to the sixth embodiment of the present invention is the radiographic image capturing device according to the third embodiment, wherein the second ventilation portion is disposed below the medium discharge path and formed in the medium discharge path. And a medium discharge distribution channel for discharging a part of the cooling medium discharged through the medium discharge path.

  In the radiographic imaging device according to the sixth embodiment, since the medium discharge flow path is provided below the medium discharge path via the second ventilation portion formed in the medium discharge path, The cooling medium is discharged by diverting from the path to the medium discharge path and the medium discharge distribution flow path in two directions. For this reason, since the stagnation of the flow of the cooling medium is further effectively suppressed, the cooling efficiency is further improved.

  A radiographic image capturing apparatus according to a seventh embodiment of the present invention is the radiographic image capturing apparatus according to the sixth embodiment, which is disposed in the medium discharge channel and is supplied to at least the signal conversion circuit board and the image processing circuit board. The power supply circuit board which has the function to produce | generate the power supply to be provided is provided.

  In the radiographic imaging device according to the seventh embodiment, since the power supply circuit board is provided in the medium supply flow path, the heat generated by the operation of the power supply circuit board is absorbed by the discharged cooling medium. . For this reason, it is effectively suppressed or prevented that the power supply circuit board becomes a heat source and damages the radiation detection panel.

In the radiographic image capturing device according to the eighth embodiment of the present invention, in the radiographic image capturing device of any of the first, third, and fourth embodiments, the medium feeding is performed on one end side of the medium feeding path. An intake fan for supplying the cooling medium is provided in the path, and an exhaust fan for discharging the cooling medium in the medium discharge path is provided in the medium discharge path.

  According to the radiographic imaging device according to the eighth embodiment, since the intake fan is provided on one end side of the medium feeding path, the efficiency of feeding the cooling medium into the medium feeding path is improved. Furthermore, since the exhaust fan is provided in the medium discharge path, the cooling medium discharge efficiency from the medium discharge path is improved. For this reason, since the stagnation of the flow of the cooling medium is effectively suppressed, the cooling efficiency is improved.

  In the radiographic imaging device according to the ninth exemplary embodiment of the present invention, in the radiographic imaging device according to the eighth exemplary embodiment, the cooling medium is provided downstream of the intake fan on one end side of the medium supply path. A cross flow fan for feeding is provided.

  According to the radiographic imaging apparatus according to the ninth embodiment, the cross flow fan is provided on the downstream side of the intake fan on one end side of the medium feeding path, and the cooling medium is provided in the medium feeding path by the cross flow fan. Will be sent. In the cross flow fan, the cooling medium feeding width is wide and the cooling medium can be fed with a uniform feeding amount, so that the cooling efficiency is improved.

Radiographic imaging apparatus according to the tenth embodiment of the present invention, the first embodiment, the third embodiment, fourth embodiment, the radiation imaging apparatus according to any one of the sixth embodiment to ninth embodiment, The cooling medium diverting portion is configured by a V-shaped deflecting plate that spreads from one end side to the other end side of the medium feeding path.

  In the radiographic image capturing apparatus according to the tenth embodiment, the cooling medium diverting portion is constituted by a polarizing plate, and this polarizing plate has a V-shape that spreads from one end side to the other end side of the medium feeding path. For this reason, the cooling medium flowing in the medium feeding path is diverted by the polarizing plate, and the flow of the cooling medium is deflected toward the signal conversion circuit board side disposed on both sides of the medium feeding path.

  In the radiographic image capturing device according to the eleventh embodiment of the present invention, in the radiographic image capturing device according to the tenth embodiment, the deflecting plate is formed in a curved shape that is convex toward the facing side.

  According to the radiographic imaging device according to the eleventh embodiment, since it is configured by a curved shape that protrudes toward the side where the polarizing plate faces, the resistance of the flow of the cooling medium during the diversion is reduced. For this reason, since the stagnation of the flow of the cooling medium is effectively suppressed, the cooling efficiency is improved.

The radiographic imaging apparatus according to the twelfth embodiment of the present invention includes a radiation detection panel, a signal conversion circuit board, a medium feeding path , a cooling medium diverting section, and a medium discharging path of the radiographic imaging apparatus according to the first embodiment. Provided between the imaging surface and the radiation irradiating unit, the imaging table disposed on at least the inside of the housing, the imaging table whose surface on the radiation detection panel is the imaging surface, the radiation irradiation unit provided on the imaging surface A compression plate.

  In the radiographic image capturing apparatus according to the twelfth embodiment, in a mammography having an imaging table, a radiation irradiating unit, and a compression plate, the same effects as those obtained by the radiographic image capturing apparatus according to the first to eleventh embodiments are obtained. can get.

  The radiographic imaging apparatus according to the present invention has an excellent effect that the cooling effect of the signal conversion circuit board serving as a heat source can be enhanced to effectively suppress or prevent damage to the radiation detection panel.

It is a schematic side view explaining the whole structure of the radiographic imaging apparatus which concerns on 1st Embodiment of this invention. It is a block circuit diagram of the principal part of the radiographic imaging apparatus shown by FIG. It is a block circuit diagram of the principal part of the radiographic imaging apparatus shown by FIG. It is a top view which shows a part inside imaging | photography stand of the radiographic imaging apparatus shown by FIG. It is a schematic side view which shows a part inside imaging | photography stand shown by FIG. FIG. 6 is a perspective view in which a part of the inside of the photographing stand shown in FIGS. FIG. 7 is a perspective view of an imaging stand corresponding to FIG. 6 with some components removed. FIG. 8 is an enlarged cross-sectional view of a part of the imaging stand taken along line F8-F8 shown in FIGS. 6 and 7 and viewed from the direction of the arrows. FIG. 5 is a perspective view of some components inside the imaging stand shown in FIG. 4 and the like. It is a perspective view which expands and shows the component shown by FIG. It is a perspective view which expands and shows a part of component inside the imaging | photography stand shown by FIG. FIG. 12 is an enlarged side view of the component shown in FIG. 11. FIG. 8 is a perspective view of some components inside the photographing stand shown in FIGS. 6 and 7 and the like. It is a top view corresponding to FIG. 4 which shows a part inside imaging | photography stand of the radiographic imaging apparatus which concerns on 2nd Embodiment of this invention. It is a top view corresponding to FIG. 4 which shows a part of imaging | photography stand inside the radiographic imaging apparatus which concerns on 3rd Embodiment of this invention. It is a top view corresponding to FIG. 14 which shows a part inside imaging | photography stand of the radiographic imaging apparatus which concerns on the modification of 3rd Embodiment.

  Embodiments according to the present invention will be described below with reference to the accompanying drawings. In the drawings, components having the same function are denoted by the same reference numerals, and overlapping descriptions are omitted as appropriate. In addition, a direction that is appropriately shown in the drawing and that is marked with a symbol X indicates a direction from the left side to the right side when viewed from a subject (photographer) in a state of facing the radiographic imaging apparatus for radiography. ing. Similarly, the direction with the symbol Y indicates the direction from the front side (chest wall side) of the subject toward the back side of the radiographic imaging device, and the direction with the symbol Z indicates the feet of the subject. The direction from the lower side to the upper side of the radiographic apparatus is shown. That is, the symbols X, Y, and Z are directions that coincide with the X, Y, and Z axes in the XYZ coordinates.

[First Embodiment]
The first embodiment of the present invention describes an example in which the present invention is applied to a mammography as a radiographic image capturing apparatus and an imaging stand incorporated therein.

(Overall configuration of radiographic imaging device)
As shown in FIG. 1, the radiographic image capturing apparatus 10 according to the first embodiment is a mammography. The radiographic imaging apparatus 10 is configured to capture a breast (subject to be imaged) of a subject in a standing position by irradiation with radiation. In the radiographic imaging device 10, the breasts of a subject in a sitting position sitting on a chair such as a wheelchair and a subject in which only the upper body is in a standing state can be separately photographed on the left and right.

  The radiographic image capturing apparatus 10 is disposed on the front side (chest wall of the subject) and has an imaging unit 12 having a substantially C shape in a side view, and is disposed closer to the Y direction (rear side) than the imaging unit 12. And a base part 14 that supports the photographing part 12 from the back side. The imaging unit 12 includes an imaging table 16, a holding unit 18, a compression plate 20, and a support unit 22 in the Z direction from the lower side toward the upper side. An imaging surface 24 is provided at the uppermost portion of the imaging table 16 so that the lower part of the subject's breast comes into contact therewith. Although the shape is not particularly limited, here, the shape of the imaging surface 24 in a plan view is a trapezoid that slightly widens from the chest wall side toward the back side. From the viewpoint of radiation transmission and mechanical strength, at least the imaging surface 24 is formed of, for example, carbon fiber reinforced plastic. A photographing table 16 is supported below the holding unit 18. A compression plate 20 is supported on the upper side of the photographic stand 16 of the holding unit 18 via a support arm 26.

  The compression plate 20 is configured to sandwich a breast with the imaging surface 24 and compress the breast from the top side. The compression plate 20 is formed of a hollow bottomed rectangular column that is open at the top. Although not particularly provided in the first embodiment, a lid member that closes the opened upper portion may be provided on the compression plate 20. The compression plate 20 is movable in the vertical direction (Z direction) with respect to the imaging surface 24. The support arm 26 is provided with a rotation shaft (not shown), and the compression angle of the compression plate 20 can be adjusted around the rotation shaft.

  The support portion 22 is provided above the holding portion 18 as a separate component, and has a substantially inverted L shape in side view. On the upper side of the support portion 22, a radiation irradiating portion 28 that can irradiate radiation for photographing or measurement toward the photographing surface 24 is provided. A radiation detection panel 30 serving as a radiation detector, which will be described later, is provided inside the imaging table 16 facing the radiation irradiation unit 28. In the radiation detection panel 30, image information is detected by being irradiated with radiation that passes through the compression plate 20, the breast, and the imaging surface 24 from the radiation irradiation unit 28 and carries image information of the breast. In the radiographic image capturing apparatus 10 according to the present embodiment, X-rays are used as radiation. The present invention is not limited to X-rays as radiation. For example, the radiation includes at least gamma rays, electron beams, neutron beams, proton beams, heavy particle beams and the like used for medical treatment.

  A rotation shaft (not shown) that extends in the horizontal direction toward the front side is provided at the intermediate portion in the vertical direction of the base portion 14. A support portion 22 and a holding portion 18 are rotatably supported on the rotation shaft. That is, the imaging unit 12 including the support unit 22 is rotatable with respect to the base unit 14 with the rotation axis as the rotation center.

(System configuration of radiographic imaging device)
As shown in FIG. 2, in the radiographic imaging device 10 according to the first exemplary embodiment, the radiation irradiation unit 28, the radiation detection panel 30, the signal conversion circuit board 44, the image processing circuit board 50, and the power supply including the power supply unit A radiographic image generation system is constructed by including a circuit built in the imaging stand 16 such as the circuit board 62 and the console 80.

(Circuit configuration of radiation irradiation unit)
The radiation irradiation unit 28 includes a radiation source 70, a radiation source control unit 72, and a communication unit 74. The communication unit 74 transmits and receives various information such as exposure conditions to and from the console 80. In the radiation source controller 72, the radiation source 70 is controlled based on the exposure conditions received via the communication unit 74. The radiation source control unit 72 is provided with a microcomputer, and information such as the exposure condition received via the communication unit 74 is stored in the memory of the microcomputer. The exposure conditions include at least information including, for example, tube voltage, tube current, and exposure time. Based on such exposure conditions, the radiation source controller 72 irradiates radiation from the radiation source 70. Be controlled.

(Circuit configuration inside the camera stand)
The radiation detection panel 30 incorporated in the imaging stand 16 includes a plurality of scanning lines 38 extending in the scanning line extending direction, for example, the vertical direction, and arranged in the output line extending direction, for example, the horizontal direction, and the output line extending. And a plurality of output lines 40 arranged in the scanning direction and extending in the scanning direction. At the intersection of the scanning line 38 and the output line 40, there is provided a detection pixel 32 that generates a charge signal from the radiation when the radiation is incident thereon. A plurality of detection pixels 32 are arranged along each of the scanning line extending direction and the output line extending direction. The detection element 32 includes a conversion unit 34 that generates a charge signal when radiation is incident, and a switch unit 36 that controls conduction and non-conduction between the output line 40 and the conversion unit 34 by a scanning line 38. I have. The radiation detection panel 30 according to the present embodiment employs a direct conversion FPD, and amorphous selenium is used for the conversion unit 34 of the detection pixel 32, for example.

  Further, inside the imaging stand 16, there are a gate driver 42, a signal conversion circuit board 44, an image processing circuit board 50, a power supply circuit board 62 including a power supply unit, and a high voltage device 60 including a high voltage generation unit. The fan control unit 64 is provided.

  The gate driver 42 is connected to a scanning line 38 provided on the radiation detection panel 30. Here, as shown in FIGS. 6 and 9 to be described later, the radiation detection panel 30 has a rectangular shape in plan view, and the gate driver 42 is arranged along one side of the back side of the radiation imaging apparatus 10. It is installed.

  The signal conversion circuit board 44 is connected to an output line 40 provided in the radiation detection panel 30 and has a function as a charge amplifier that converts a charge signal generated by the conversion unit 34 of the detection element 32 into a voltage signal. ing. As shown in FIG. 3, the signal conversion circuit board 44 includes a sample hold circuit 46, a multiplexer 47, and an analog / digital (A / D) converter 48.

  The sample hold circuit 46 is disposed for each output line 40 and includes an operational amplifier 46A, a capacitor 46B, and a switch 46C. Both the capacitor 46B and the switch 46C are electrically connected in parallel between the input and output of the operational amplifier 46A. The charge signal transmitted from the detection element 32 through the output line 40 is held in the sample hold circuit 46. The sample hold circuit 46 converts the charge signal into an analog signal (voltage signal) by the operational amplifier 46A and the capacitor 46B. The switch 46C of the sample and hold circuit 46 is used as a reset circuit that discharges the charge signal stored in the capacitor 46B. The analog signal converted in the sample hold circuit 46 is serially input to the multiplexer 47. The multiplexer 47 serially outputs an analog signal to the analog / digital converter 48. The analog / digital converter 48 converts an analog signal into a digital signal.

  Here, the signal conversion circuit board 44 has one side where the gate driver 42 is provided and both sides facing the radiation detection panel 30 different from the one side on the chest wall side (the right side and the left side when viewed from the subject). Are divided into signal conversion circuit boards 44A and 44B, respectively. The arrangement pitch of the sample hold circuits 46 mounted on the signal conversion circuit board 44 in the same direction is larger than the arrangement pitch of the detection elements 32 in the scanning line extending direction. For this reason, signal conversion circuit boards 44A and 44B are provided on opposite sides of the radiation detection panel 30, and output lines 40 arranged in the scanning line extending direction are alternately connected to the signal conversion circuit boards 44A and 44B. As a configuration, the size and the density of the detection element 32 are reduced. Further, since the radiation detection panel 30 is disposed in the vicinity of the subject, a space for disposing the signal conversion circuit board 44 is not secured on the side of the radiation detection panel 30.

  As shown in FIG. 2, the image processing circuit board 50 includes a signal processing unit 52, a detector control unit 54, an image memory 56, and a communication unit 58. In the signal processing unit 52, image processing is performed on the digital signal converted through the signal conversion circuit board 44 to generate radiation image information. The signal processing unit 52 is connected to the image memory 56, and the radiation image information generated in the signal processing unit 52 is serially stored in the image memory 56. The image memory 56 has a storage capacity capable of storing a predetermined number of pieces of radiographic image information, and radiographic image information obtained by imaging is sequentially stored in the image memory 206 every time radiographic images are captured.

  The detector control unit 54 is connected to each of the gate driver 42, the signal processing unit 52, the image memory 56, the communication unit 58, the power supply unit, and the high voltage generation unit, and controls them. The detector control unit 54 includes a microcomputer, and the microcomputer is constructed by including a CPU (Central Processing Unit), a memory such as a RAM and a ROM, and a storage unit such as a hard disk.

  The communication unit 58 transmits / receives various information to / from an external device based on control from the detector control unit 54. Although not limited to this format, the communication unit 58 according to the first embodiment is a wireless local area network (Local Area Network) represented by IEEE (Institute of Electrical and Electronics Engineers) 802.11a / b / g. ) A wireless communication unit corresponding to the standard. Specifically, the communication unit 58 transmits and receives various types of information for performing control related to radiographic image capturing between the detector control unit 54 and the console 80, and transmits radiation image information from the detector control unit 54 to the console 80. Etc. are performed by wireless communication.

  The power supply unit of the power supply circuit board 62 is configured to supply power to various circuits such as the gate driver 42, the signal conversion circuit board 44, and the image processing circuit board 50. The high voltage generator 60 is configured to supply a high voltage to the converter 34 of the radiation detection panel 30. The fan control unit 64 controls the driving of an intake fan, an exhaust fan, and a cross flow fan, which will be described later.

(Console circuit configuration)
As shown in FIG. 2, the console 80 is constructed as a server computer and includes a display 80A and an operation panel 80C. The display 80A is a monitor that displays an operation menu of the radiation image capturing apparatus 10, a captured radiation image, and the like. The operation panel 80C includes a plurality of operation keys, switches, and the like, and can input various information and operation instructions. The console 80 includes a CPU 80E, a ROM 80F, a RAM 80G, a hard disk drive (HDD) 80H, a display driver 80B, an operation input detection unit 80D, and a communication unit 82.

(Internal structure of the shooting stand)
In the imaging stand 16 of the radiographic image capturing apparatus 10 according to the first exemplary embodiment, as shown in FIGS. 4 to 10, the entire contour is formed by a hollow cubic housing 100. The casing 100 is made of a material such as carbon fiber reinforced plastic (CFRP), aluminum, steel plate, or the like whose surface is insulated as necessary.

  In the upper stage of the imaging surface 24 side of the imaging table 16, the cooling medium 102 is fed from one end on the back side (reference numeral 104A in FIG. 5) to the other end on the chest wall side (reference numeral 104B in FIG. 5). A feeding path 104 is provided. A radiation detection panel 30 is disposed above the medium feeding path 100 (on the imaging surface 24 side), and the back surface of the radiation detection panel 30 is used as a part of the upper wall of the medium feeding path 100. Yes. Although illustration is omitted, in practice, a heat insulating material is provided between the medium feeding path 100 and the radiation detection panel 30.

  A signal conversion circuit board 44A is disposed on one of the left sides when viewed from the subject on both sides of the medium feeding path 104 parallel to the feeding direction of the cooling medium 102, and the right side when viewed from the subject. On the other side, a signal conversion circuit board 44B is provided. Both the signal conversion circuit board 44A and the signal conversion circuit board 44B have the same configuration. In the first embodiment, the signal conversion circuit board 44 is a flexible circuit board in which a sample hold circuit 46, a multiplexer 47, and an analog-digital converter 48 are mounted on a base film 44D as an integrated circuit (IC chip) 44C. ing. One end on the upper side of the signal conversion circuit board 44 is electrically and mechanically connected to the side portion of the radiation detection panel 30, and the other end on the lower side is electrically and mechanically connected to the image processing circuit board 50. Has been. A plurality of signal conversion circuit boards 44 </ b> A are arranged along one side of the radiation detection panel 30 from the chest wall side to the back side, and the signal conversion circuit board 44 </ b> B is arranged along the other side of the radiation detection panel 30 facing each other. A plurality are arranged from the chest wall side to the back side. The signal conversion circuit board 44 is used as part of both side walls of the medium feeding path 100.

  As shown in FIGS. 4, 5, 7, and 8 to 11, the signal conversion circuit board 44 protrudes in the medium feeding path 104 and generates heat due to the operation of the signal conversion circuit board 44. Is provided from the signal conversion circuit board 44. As shown in FIGS. 11 and 12, the heat sink 110 is configured by arranging a plurality of substantially horizontal plate-like heat radiation fins 110A extending in the vertical direction from the chest wall side to the back side in a substantially parallel manner. ing. The number of the radiating fins 110A is not particularly limited, but for example, 3 to 5 is the optimum number. The heat sink 110 is made of a material such as aluminum or copper having excellent thermal conductivity and excellent workability. Further, as shown in FIG. 8, the heat sink 110 is attached to the integrated circuit 44 </ b> C of the signal conversion circuit board 44 via the adhesive layer 112. For example, a heat transfer gel is used for the adhesive layer 112. The back surface of the base film 44D of the signal conversion circuit board 44 opposite to the surface on which the integrated circuit 44C is mounted is fixed to an inner frame 116 provided along the inner wall of the housing 100 through an adhesive layer 114. ing. As with the adhesive layer 112, a heat transfer gel is used for the adhesive layer 116.

  A flat partition frame 118 attached to the side wall of the housing 100 is provided below the medium feeding path 104. The partition frame 118 is made of a material such as aluminum or steel plate. The partition frame 118 is used as a part of the bottom wall of the medium feeding path 104.

  As shown in FIG. 4 to FIG. 7, in the medium feeding path 104, a cooling medium diverting unit 120 that diverts the cooling medium 102 and guides it to the signal conversion circuit board 44 </ b> A and the signal conversion circuit board 44 </ b> B is provided. ing. The cooling medium diverting unit 120 includes a deflection plate 120A and a deflection plate 120B that form a V shape that expands in a plan view from the back side of the medium feeding path 104 to the chest wall side. Here, a deflecting plate 120C extending in a direction substantially orthogonal to the feeding direction of the cooling medium 102 is also provided on the chest wall side, and the shape of the cooling medium diverting portion 120 in a plan view is a triangle. Each of the deflection plates 120 </ b> A to 120 </ b> C has an L-shaped cross section in which a lower portion of a flat plate that is flat in the horizontal direction and the vertical direction is bent in the horizontal direction, and the bent portion is fixed to the surface of the partition frame 118. ing. Although the material is not particularly limited, the deflection plates 120A to 120C are formed of a material such as aluminum, a steel plate, or a resin.

  As shown in FIGS. 6 and 9, a gate driver 42 is provided above the medium feeding path 104 and on the back side of the radiation detection panel 30. Further, as shown in FIGS. 6 and 7, a high voltage generator 60 is provided above the medium feeding path 104 and on the back side of the gate driver 42.

  As shown in FIGS. 4 to 7 and 13, below the medium feeding path 104, the medium feeding path 104 is connected to the medium feeding path 104 via a first ventilation portion 118 </ b> A formed on the chest wall side of the medium feeding path 104. A medium discharge path 130 for discharging the supplied cooling medium 102 is provided. 118 A of 1st ventilation | gas_flowing parts are penetrated and formed in the substantially rectangular shape by the partition frame 118 in planar view. The medium discharge path 130 is located in the middle stage of the imaging table 16 and discharges the cooling medium 102 from the chest wall side to the back side.

  As shown in FIGS. 5 to 7, a partition frame 118 is provided above the medium discharge path 130, and this partition frame 118 is used as a part of the upper wall of the medium discharge path 130. Yes. A partition frame 132 having substantially the same configuration as the partition frame 118 is provided below the medium discharge path 130, and the partition frame 132 is used as a part of the bottom wall of the medium discharge path 130. The side wall of the housing 100 is used as the side wall of the medium discharge path 130. A partition frame 132C extends from the back side of the partition frame 118 to between an intake fan 150 and an exhaust fan, which will be described later. The partition frame 132 </ b> C is configured as a partition plate that separates the medium feeding path 104 and the medium discharging path 130.

  As shown in FIGS. 4 to 7 and FIG. 13, an image processing circuit board 50 is disposed inside the medium discharge path 130. Here, the image processing circuit board 50 is attached to the back side of the partition frame 118 at a location facing the radiation detection panel 30. The image processing circuit board 50 has a substrate through-hole 50A that passes through a part of the image processing circuit board 50 and overlaps the first vent 118A and discharges the cooling medium 102 from the first vent 118A to the medium discharge path 130. Is provided.

  As shown in FIGS. 6 and 7, further below the medium discharge path 130, the medium discharge path 130 is discharged to the medium discharge path 130 via the second ventilation portion 132 </ b> A formed on the chest wall side of the medium discharge path 130. A medium supply / distribution flow path 140 that distributes and discharges a part of the cooled cooling medium 102 is disposed. The second ventilation portion 132A is formed to penetrate the partition frame 132 in a substantially rectangular shape in plan view. The medium supply / distribution flow path 140 is located at the lower stage of the imaging table 16 and merges with the cooling medium 102 discharged through the third ventilation portion 132B formed on the back side of the medium discharge path 130, so that the chest wall side The cooling medium 102 is discharged from the rear side. A part of the partition frame 132 crosses between the second ventilation part 132A and the third ventilation part 132B, and the rigidity of the partition frame 132 is enhanced.

  A partition frame 132 is provided on the upper side of the medium supply / distribution flow path 140, and the partition frame 132 is used as a part of the upper wall of the medium discharge / distribution flow path 140. A partition frame 142 having substantially the same configuration as the partition frame 132 is provided below the medium discharge path 140, and the partition frame 142 is used as a part of the bottom wall of the medium discharge flow path 140. . The side wall of the casing 100 is used as the side wall of the medium discharge flow path 140.

  As shown in FIG. 6, the power supply circuit board 62 is disposed inside the medium discharge flow path 140. Here, the power supply circuit board 62 is mounted on a support table 144 shown in FIG. 7 in the middle of the partition frame 132 and the partition frame 142 at a location facing the radiation detection panel 30 and the image processing circuit board 50. .

  As shown in FIGS. 4, 6, and 7, an intake fan 150 that feeds the cooling medium 102 into the medium feeding path 104 is provided on the back side of the medium feeding path 104. A propeller fan is used as the intake fan 150. An exhaust fan 152 that exhausts the cooling medium 102 in the medium discharge path 130 and the medium discharge distribution path 140 is provided on the back side of the medium discharge path 130 and the medium discharge distribution path 140. Like the intake fan 150, a propeller fan is used as the exhaust fan 152.

Further, a cross flow fan 154 that feeds the cooling medium 102 to the medium feeding path 104 is provided on the rear side of the medium feeding path 104 on the downstream side of the intake fan 150.
(Operation and effect of the first embodiment)

  As described above, in the radiographic imaging device 10 according to the present exemplary embodiment, the charge signal generated from the radiation by the radiation detection panel 30 is converted into a voltage signal by the signal conversion circuit board 44. Since the radiation detection panel 30 is disposed above the medium feeding path 104 and the signal conversion circuit boards 44 are disposed on both sides of the medium feeding path 104, the radiation detection panel 30 and the signal conversion circuit board are disposed. The distance to 44 is shortened, and noise is difficult to ride on the charge signal.

  Here, the signal conversion circuit board 44 is disposed on both sides of the medium feeding path 104 in parallel with the feeding direction of the cooling medium 102, and the cooling medium diverting section 120 is provided in the medium feeding path 104. It has been. The cooling medium diverting unit 120 diverts the cooling medium 102 and guides it to the signal conversion circuit board 44. For this reason, since the cooling medium 102 flows along the signal conversion circuit board 44, the heat generated by the operation of the signal conversion circuit board 44 is absorbed by the cooling medium 102. If amorphous selenium is used for the conversion unit 34 of the radiation detection panel 30, the amorphous selenium is altered at an environmental temperature of about 33 degrees.

  Therefore, according to the radiographic imaging device 10 according to the present exemplary embodiment, it is possible to enhance the cooling effect of the signal conversion circuit board 44 serving as a heat source and effectively suppress or prevent damage to the radiation detection panel 30.

  In the radiographic imaging apparatus 10 according to the present exemplary embodiment, the medium discharge path 130 is provided below the medium supply path 104 via the first ventilation portion 118A formed at the other end of the medium supply path 104. The cooling medium 102 is discharged from the medium feeding path 104 to the medium discharging path 130 in one direction. For this reason, since the stagnation of the flow of the cooling medium 102 is effectively suppressed, the cooling efficiency is improved.

  Furthermore, in the radiographic imaging device 10 according to the present exemplary embodiment, since the image processing circuit board 50 is provided in the medium discharge path 130, heat generated by the operation of the image processing circuit board 50 is discharged. Absorbed by the cooling medium 102. For this reason, it is effectively suppressed or prevented that the image processing circuit board 50 becomes a heat generation source and damages the radiation detection panel 30.

  Further, in the radiographic imaging apparatus 10 according to the present exemplary embodiment, the substrate penetrating part 50A is provided in a part of the image processing circuit board 50. Therefore, the cooling medium extending from the first ventilation part 118A to the medium discharge path 130. The cross-sectional area perpendicular to the discharge direction of 102 (the cross-sectional area through which the cooling medium 102 flows) is increased. For this reason, since the stagnation of the flow of the cooling medium 102 is effectively suppressed, the cooling efficiency is improved. Further, since the cooling medium 102 flows along the image processing circuit board 50 from the substrate penetrating portion 50A, the image processing circuit board 50 is cooled from the central portion, and the cooling efficiency of the image processing circuit board 50 is improved.

  Furthermore, in the radiographic imaging apparatus 10 according to the present exemplary embodiment, since the heat sink 110 that releases heat from the signal conversion circuit board 44 is provided in the medium feeding path 104, the cooling efficiency of the signal conversion circuit board 44 is improved. Is improved.

  Further, in the radiographic imaging apparatus 10 according to the present exemplary embodiment, the medium discharge flow path 140 is provided below the medium discharge path 130 via the second ventilation portion 132A formed in the medium discharge path 130. Therefore, the cooling medium 102 is discharged by diverting from the medium feeding path 104 to the medium discharging path 130 and the medium discharging branch path 140 in two directions. For this reason, since the stagnation of the flow of the cooling medium 102 is further effectively suppressed, the cooling efficiency is further improved.

  Furthermore, in the radiographic imaging device 10 according to the present exemplary embodiment, since the power supply circuit board 62 is provided in the medium discharge flow path 140, heat generated by the operation of the power supply circuit board 62 is discharged. Absorbed by the cooling medium 102. For this reason, it is possible to effectively suppress or prevent the power supply circuit board 62 from being a heat source and damaging the radiation detection panel 30.

  Moreover, in the radiographic imaging device 10 according to the present exemplary embodiment, the intake fan 150 is provided on one end side of the medium feeding path 104, so that the feeding efficiency of the cooling medium 102 into the medium feeding path 104 is improved. Be improved. Furthermore, since the exhaust fan 152 is provided in the medium discharge path 130, the efficiency of discharging the cooling medium 102 from the medium discharge path 130 is improved. For this reason, since the stagnation of the flow of the cooling medium 102 is effectively suppressed, the cooling efficiency is improved.

  Furthermore, according to the radiographic imaging device 10 according to the present exemplary embodiment, the cross flow fan 154 is provided on the downstream side of the intake fan 150 on one end side of the medium feeding path 104, and the cross flow fan 154 The cooling medium 102 is supplied to the medium supply path 104. In the cross-flow fan 154, since the feeding width of the cooling medium 102 is wide and the cooling medium 102 can be fed with a uniform feeding amount, the cooling efficiency is improved.

  Further, in the radiographic imaging apparatus 10 according to the present exemplary embodiment, the cooling medium diverting unit 120 is configured by the polarizing plates 120A and 120B, and the polarizing plates 120A and 120B are connected from one end side to the other end of the medium feeding path 104. It has a V-shape that spreads toward the side. Therefore, the cooling medium 102 flowing in the medium feeding path 104 is divided by the polarizing plates 120A and 120B, and the cooling medium is directed toward the signal conversion circuit board 44 disposed on both sides of the medium feeding path 104. The flow of 102 is deflected.

  Furthermore, in the radiographic imaging device 10 according to the present exemplary embodiment, the same operational effects as the above-described operational effects can be obtained in the mammography including the imaging table 16, the radiation irradiation unit 28, and the compression plate 20.

[Second Embodiment]
In the second embodiment of the present invention, an example in which the shape of the cooling medium distribution unit 120 of the radiographic image capturing apparatus 10 according to the first embodiment is changed will be described.

(Configuration of cooling medium diverter)
As shown in FIG. 14, in the radiographic imaging device 10 according to the second exemplary embodiment, the deflecting plate 120A and the deflecting plate 120B of the cooling medium diverting unit 120 are convex on the facing side, particularly on the upstream side of the diverting start. It is comprised by the curved shape which becomes. On the downstream side of the deflecting plate 120A and the deflecting plate 120B, a curved shape that is concave on the opposite side is formed. In plan view, each of the deflection plate 120A and the deflection plate 120B has an S-shape.

  According to the radiographic image capturing apparatus 10 according to the present embodiment, since the deflecting plate 120A and the deflecting plate 120B are configured to have a curved shape that is convex toward the facing side, the resistance of the flow of the cooling medium 102 at the time of branching Is reduced. For this reason, since the stagnation of the flow of the cooling medium 102 is effectively suppressed, the cooling efficiency is improved.

[Third Embodiment]
In the third embodiment of the present invention, an example in which the structure of the cooling medium diverting unit 120 of the radiographic imaging apparatus 10 according to each of the first and second embodiments is changed will be described.

(Configuration of cooling medium diverter)
As shown in FIG. 15, in the radiographic image capturing device 10 according to the third exemplary embodiment, the deflection plate 120 </ b> A and the deflection plate 120 </ b> B of the cooling medium distribution unit 120 protrude from the surface toward the medium feed path 104 side. Protruding portion 120D is provided. The protrusion 120D has a fin shape here, and the surface areas of the deflection plate 120A and the deflection plate 120B are increased.

  According to the radiographic imaging apparatus 10 according to the present exemplary embodiment, the surface areas of the deflecting plate 120A and the deflecting plate 120B of the cooling medium diverting unit 120 are increased by the protrusions 120D, so that the cooling diverted by the cooling medium diverting unit 120 is performed. The medium 102 itself is cooled. For this reason, since the cooling medium 102 is cooled on the upstream side, the cooling efficiency of the signal conversion circuit board 44 and the like disposed on the downstream side of the cooling medium diverting portion 120 is further improved.

(Modification)
As shown in FIG. 16, in the radiographic imaging device 10 according to the modification of the third embodiment, the deflection plate 120A and the deflection of the cooling medium diverting unit 120 are the same as the cooling medium diverting unit 120 shown in FIG. A protrusion 120D is provided on the plate 120B. In the radiographic image capturing apparatus 10 according to this modification, the same operational effects as those obtained by the radiographic image capturing apparatus 10 according to the third embodiment can be obtained.

(Other embodiments)
As mentioned above, although this invention was demonstrated using several embodiment, this invention is not limited to the said embodiment, In the range which does not deviate from a summary, it can change variously. For example, the present invention is not limited to mammography, but can be widely applied to a radiographic imaging apparatus having an imaging table cooling system.

DESCRIPTION OF SYMBOLS 10 Radiographic imaging apparatus 16 Imaging stand 20 Compression board 28 Radiation irradiation part 30 Radiation detection panel 44 Signal conversion circuit board 50 Image processing circuit board 50A Substrate penetration part 62 Power supply circuit board 100 Case 102 Cooling medium 104 Medium feed path 110 Heat sink 118A 1st ventilation part 120 Cooling medium distribution part 120A-120C Deflection plate 130 Medium discharge path 132A 2nd ventilation part 140 Medium discharge distribution path 150 Intake fan 152 Exhaust fan 154 Cross flow fan

Claims (12)

A medium feeding path through which a cooling medium is fed from one end to the other;
A radiation detection panel disposed above the medium feed path and generating a charge signal from the radiation;
A signal conversion circuit board disposed on both sides of the medium feeding path parallel to the cooling medium feeding direction and having a function of converting the charge signal into a voltage signal;
A cooling medium diverting section provided in the medium feeding path, and diverting the cooling medium and guiding the cooling medium to the signal conversion circuit board side;
A medium that is disposed below the medium feeding path and from which the cooling medium fed to the medium feeding path is discharged via a first vent formed at the other end of the medium feeding path. Drainage channel,
A radiographic imaging apparatus comprising: A medium feeding path through which a cooling medium is fed from one end to the other ;
A radiation detection panel disposed above the medium feed path and generating a charge signal from the radiation;
A signal conversion circuit board disposed on both sides of the medium feeding path parallel to the cooling medium feeding direction and having a function of converting the charge signal into a voltage signal;
A V-shaped deflecting plate is provided in the medium feeding path and extends from one end side to the other end side of the medium feeding path, and the cooling medium is diverted to the signal conversion circuit board side. A cooling medium diverting section that guides;
Ray imaging apparatus release equipped with. The radiographic image capturing apparatus according to claim 1 , further comprising an image processing circuit board disposed in the medium discharge path and having an image processing function of generating a radiographic image from the voltage signal.   4. The radiographic imaging apparatus according to claim 3, further comprising a substrate penetrating portion that penetrates a part of the image processing circuit board and discharges the cooling medium from the first ventilation portion to the medium discharge path.   The radiographic imaging apparatus of any one of Claims 1-4 provided with the heat sink which discharge | releases the heat | fever from the said signal conversion circuit board in the said medium feeding path. A portion of the cooling medium that is disposed below the medium discharge path and is discharged through the medium discharge path is divided and discharged via a second ventilation portion formed in the medium discharge path. The radiographic image capturing device according to claim 3 , further comprising a medium discharge flow channel.   The radiographic imaging of Claim 6 provided with the power supply circuit board which has a function which produces | generates the power supplied at least to the said signal conversion circuit board and the said image processing circuit board, which is arrange | positioned in the said medium discharge flow path. apparatus. An exhaust fan for supplying the cooling medium into the medium supply path is provided on one end side of the medium supply path, and exhaust for discharging the cooling medium in the medium discharge path to the medium discharge path. The radiographic imaging apparatus of any one of Claim 1, Claim 3, and Claim 4 provided with the fan.   The radiographic image capturing apparatus according to claim 8, wherein a cross-flow fan that supplies the cooling medium to the medium supply path is provided downstream of the intake fan on one end side of the medium supply path. The cooling medium diverting portion is constituted by a V-shaped deflecting plate that widens from one end side to the other end side of the medium feeding path . Item 10. The radiographic image capturing device according to any one of Items 9 to 9 .   The radiographic image capturing apparatus according to claim 10, wherein the deflecting plate has a curved shape that is convex toward the facing side. The radiation detection panel according to claim 1 , the signal conversion circuit board, the medium feeding path , the cooling medium diverting portion, and the medium discharging path are disposed at least inside the housing, and the radiation detection A shooting table whose surface on the panel is the shooting surface;
A radiation irradiation unit provided on the imaging surface;
A compression plate provided between the imaging surface and the radiation irradiation unit;
A radiographic imaging apparatus comprising:

Images