JP2010259577A - Radiographic image photographing system, radiation detecting apparatus, program, temperature control method for electronic part and radiographic image photographing method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To maintain uniform temperature distribution of an electronic part by suppressing the temperature change of the electronic part. <P>SOLUTION: A radiographic image photographing system 10 comprises a case 30 made of a material that transmits radiation 12, a radiation conversion panel 18 housed within the case 30 and converting the radiation 12 transmitted through a subject 14 into a radiation image, a radiation detecting apparatus 20 housed within the case 30 and having electronic parts 66 for processing the radiographic image outputted from the radiation conversion panel 18, and a temperature adjusting means 190 which maintains the temperature of the electronic parts 66 that reach a predetermined temperature or a temperature near the predetermined temperature at the predetermined temperature or a temperature near the predetermined temperature. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to a radiation detection apparatus in which a radiation conversion panel is housed in a housing, a radiation image capturing system including the radiation detection apparatus, and a radiation image capturing method for capturing a radiation image by irradiating a subject with radiation. . The present invention also relates to a temperature control method for controlling the temperature of an electronic component that processes the radiation image output from the radiation conversion panel, and a program that is executed by a temperature adjusting unit that controls the temperature of the electronic component.

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

  On the other hand, in an operating room or the like, it is necessary to be able to immediately read out and display a radiation image from a radiation conversion panel after imaging in order to perform a quick and accurate treatment on a patient. As a radiation conversion panel that can meet such demands, a direct conversion type radiation conversion panel using a solid-state detection element that directly converts radiation into an electrical signal, or a scintillator that temporarily converts radiation into visible light, and the visible light. An indirect conversion type radiation conversion panel using a solid-state detection element that converts light into an electrical signal has been developed. Then, a radiation detection apparatus (radiation detection) is provided by housing a direct conversion type or indirect conversion type radiation conversion panel and an electronic component that performs predetermined processing on a radiation image output from the radiation conversion panel in a casing. Cassette) is configured.

  In the radiation detection apparatus, the radiation conversion panel outputs a radiation image as an analog signal of a minute charge, but the analog signal is easily affected by a slight temperature change of an electronic component, and thus is caused by the temperature change. There is a concern about the deterioration of the image quality of the radiation image.

  In order to solve such a problem, Patent Document 1 discloses that in a standing-type radiographic imaging apparatus, a fan is provided at the upper part of the casing, while an air inlet is provided at the lower part of the casing. It has been proposed to cool the inside of the housing by driving the air and sucking outside air from the suction port.

  Further, Patent Document 2 proposes that the housing be provided with a heat exchanging portion that adjusts the temperature of air in the space in the housing by heat exchange with an external heat medium.

JP 2000-37374 A JP 2007-260092 A

  However, in the technique of Patent Document 1, since the outside air is sucked from the suction port to cool the inside of the housing, the temperature inside the housing depends on the external environment temperature, and the temperature change of the electronic component is controlled with high accuracy. Can not do it.

  Further, with the technique of Patent Document 2, it is possible to suppress the temperature rise of the entire casing, but on the other hand, it is difficult to suppress a local temperature change (temperature change of electronic components) in the casing. .

  The present invention has been made in order to solve the above-described problems, and a temperature control method capable of suppressing a temperature change of an electronic component and maintaining a uniform temperature distribution of the electronic component, and the above-mentioned It is an object of the present invention to provide a program to be executed by a temperature adjusting means for adjusting the temperature of an electronic component.

  In addition, the present invention obtains a high-quality radiographic image by converting the radiation transmitted through the subject into a radiographic image in a state where the temperature change of the electronic component is suppressed and the temperature distribution of the electronic component is kept uniform. It is an object of the present invention to provide a radiation detection apparatus, a radiographic imaging system, and a radiographic imaging method that can be performed.

The radiographic imaging system according to the present invention is:
A housing made of a material that transmits radiation, a radiation conversion panel that is housed in the housing and converts the radiation transmitted through the subject into a radiation image, and is housed in the housing and output from the radiation conversion panel A radiation detection apparatus comprising an electronic component for processing the radiation image;
Temperature adjusting means for holding the temperature of the electronic component that has reached a predetermined temperature or in the vicinity of the predetermined temperature at the predetermined temperature or in the vicinity of the predetermined temperature;
It is characterized by having.

The radiation detection apparatus according to the present invention includes:
A housing made of a material that transmits radiation;
A radiation conversion panel that is housed in the housing and converts the radiation transmitted through the subject into a radiation image;
An electronic component housed in the housing and for processing the radiation image output from the radiation conversion panel;
Temperature adjusting means for holding the temperature of the electronic component that has reached a predetermined temperature or in the vicinity of the predetermined temperature at the predetermined temperature or in the vicinity of the predetermined temperature;
It is characterized by having.

The program according to the present invention is:
The radiation transmitted through the subject is converted into a radiation image by a radiation conversion panel housed in a housing made of a material that transmits radiation, and the radiation image output from the radiation conversion panel is converted by an electronic component in the housing. When processing, a program to be executed by a temperature adjusting means for controlling the temperature of the electronic component,
The temperature of the electronic component that has reached a predetermined temperature or in the vicinity of the predetermined temperature is maintained at the predetermined temperature or in the vicinity of the predetermined temperature.

An electronic component temperature control method according to the present invention includes:
The radiation transmitted through the subject is converted into a radiation image by a radiation conversion panel housed in a housing made of a material that transmits radiation, and the radiation image output from the radiation conversion panel is converted by an electronic component in the housing. When processing
The temperature of the electronic component that has reached a predetermined temperature or in the vicinity of the predetermined temperature is held by the temperature adjusting means at or near the predetermined temperature.

  The radiographic image capturing method according to the present invention provides the subject by outputting the radiation from a radiation source when the temperature of the electronic component is held at or near the predetermined temperature by the temperature control method. It is characterized by shooting for

  According to the present invention, the temperature of the electronic component that has reached the predetermined temperature or the vicinity of the predetermined temperature is maintained at the predetermined temperature or the vicinity of the predetermined temperature by the temperature adjusting means. ) And a uniform temperature distribution.

  Therefore, in a state where the temperature change of the electronic component is suppressed and the temperature distribution is uniformed by the temperature adjusting means, the radiation transmitted through the subject is converted into a radiation image by the radiation conversion panel, and the radiation conversion panel If the analog signal of the radiographic image is output to the electronic component, the influence of the temperature change of the electronic component on the analog signal can be surely reduced, so that a high-quality radiographic image can be easily acquired. Become.

It is a block diagram of the radiographic imaging system concerning this embodiment. It is a perspective view of the radiation detection apparatus of FIG. It is a perspective view of the radiation detection apparatus of FIG. FIG. 4 is a cross-sectional view taken along line IV-IV in FIG. 3. It is sectional drawing along the VV line of FIG. It is a circuit block diagram of the radiation detection apparatus of FIGS. It is a block diagram of the radiation detection apparatus of FIGS. It is a flowchart of operation | movement of the radiographic imaging system of FIG. It is a block diagram of the radiographic imaging system concerning the 1st modification. It is a block diagram of the cradle and radiation detection apparatus which comprise the radiographic imaging system which concerns on a 2nd modification. It is a block diagram of the cradle and radiation detection apparatus which comprise the radiographic imaging system which concerns on a 3rd modification. It is a perspective view of the radiation detection apparatus which comprises the radiographic imaging system which concerns on a 4th modification. It is a perspective view of the radiation detection apparatus which comprises the radiographic imaging system which concerns on a 5th modification.

  As shown in FIG. 1, the radiographic imaging system 10 according to the present exemplary embodiment transmits a radiation source 16 for irradiating a patient (subject) 14 with radiation 12 having a dose according to imaging conditions and the patient 14. A radiation detection device (radiation detection cassette) 20 that houses a radiation conversion panel 18 (see FIGS. 3 to 5) that detects the radiation 12, and a display device that displays a radiation image based on the radiation 12 detected by the radiation detection device 20 And a console (control device) 24 for controlling the radiation source 16, the radiation detection device 20, and the display device 22. Between the console 24 and the radiation source 16, the radiation detection device 20, and the display device 22, for example, UWB (Ultra Wide Band), IEEE 802.11. Signals are transmitted and received by wireless communication using WiFi (Wireless Fidelity) such as a / g / n or millimeter waves. The console 24 is connected to a radiology information system (RIS) 26 for comprehensively managing radiographic images and other information handled in the radiology department in the hospital, and the RIS 26 has medical information in the hospital. Is connected to a medical information system (HIS) 28 for overall management.

  As shown in FIGS. 2 to 5, the radiation detection apparatus 20 includes a casing (housing) 30 made of a material that transmits the radiation 12. The casing 30 includes a substantially planar first member (top plate) 34 that forms an irradiation surface (first surface) 32 of the radiation 12 in the casing 30, a frame member 36 that forms side surfaces, and a bottom surface (second surface). ) And a substantially planar second member (back plate) 40 that constitutes 38.

  As shown in FIGS. 3 to 5, the frame member 36 is fixed to the periphery of the second member 40, and the periphery of the first member 34 is fixed to the upper surface of the frame member 36. A space is formed.

  In this case, the periphery of the first member 34 is fixed to the frame member 36 so as to cover the upper surface of the frame member 36 and bend toward the periphery of the second member 40, while the periphery of the second member 40 is Is fixed to the frame member 36 so as to cover the bottom surface of the frame member 36 and to be curved toward the periphery of the first member 34. Further, each of the above-described curved portions of the first member 34 and the second member 40 is processed into an arc shape in the sectional views of FIGS. 4 and 5. Further, inside the frame member 36, a substantially planar base (a partition member) that partitions the closed space into a first chamber 42 on the first member 34 side and a second chamber 44 on the second member 40 side. 46 is formed. Furthermore, the thickness of the base 46 is larger than the thickness of the first member 34 and the thickness of the second member 40, while the plane direction of the first member 34 and the second member 40 of the frame member 36 (see FIGS. 4 and 4). The thickness along the horizontal direction in FIG. 5 is larger than the thickness of the first member 34 and the thickness of the second member 40.

  Here, the first member 34 and the second member 40 constituting the casing 30 are made of a material having a specific gravity of 2.8 or less in order to reduce the weight of the radiation detection apparatus 20 as a whole. It is comprised from any one material among the composite material containing a cellulose fiber or glass fiber, an engineering plastic, and biomass plastics. Further, the first member 34 and the second member 40 may be made of the same material, or may be made of different materials.

  Specifically, the composite material including carbon fiber is carbon fiber reinforced plastic (CFRP), the composite material including cellulose fiber is a composite material including cellulose microfibril fiber, and the composite material including glass fiber is glass. Fiber reinforced plastic (GFRP).

  In this case, for example, the first member 34 has a relatively high thermal conductivity so that the patient 14 in contact with the first member 34 does not feel heat due to self-heating of the electronic component 66 or the like in the radiation detection apparatus 20. It is desirable to be composed of a highly rigid carbon made of a low PAN (polyacrylonitrile) type carbon fiber. On the other hand, the second member 40 may be composed of strong rigid carbon made of pitch-type carbon fiber having higher thermal conductivity than PAN-type carbon fiber so that heat radiation from the radiation detection apparatus 20 to the outside is good. desirable.

  Engineering plastics include polyamide (PA), polyacetal (POM), polycarbonate (PC), modified polyphenylene ether (m-PPE, modified PPE), polybutylene terephthalate (PBT), polyethylene terephthalate (PET), glass fiber reinforced Polyethylene terephthalate (GF-PET), ultra high molecular weight polyethylene (UHPE), syndiotactic polystyrene (SPS), cyclic polyolefin (COP), polyphenylene sulfide (PPS), polysulfone (PSF), amorphous polyarylate (PAR), Polyethersulfone (PES), liquid crystal polyester (LCP), polyetheretherketone (PEEK), polyimide (PI), polyetherimide (PEI), epoxy (EP) There is.

  The frame member 36 including the base 46 is made of a material having a specific gravity of 2.8 or less in order to reduce the weight of the entire radiation detection apparatus 20. Specifically, from the material similar to the 1st member 34 and the 2nd member 40 mentioned above, ie, any one material from the composite material containing carbon fiber, a cellulose fiber, or a glass fiber, engineering plastics, and biomass plastics Composed. In addition, since the frame member 36 and the base 46 should just be comprised from the material which has a specific gravity of 2.8 or less, it may be comprised with light metal materials, such as aluminum, aluminum alloy, magnesium, or a magnesium alloy. Of course.

  As shown in FIGS. 2 and 3, the casing 30 has an octagonal shape in plan view with corners cut off at four corners, and each corner absorbs an impact caused by an external load. A shock absorbing member 48 made of rubber or the like is attached. In this case, projections 50 are provided on the corner side of the shock absorbing member 48, and the respective shock absorbing members are fitted into the holes 52 formed in the corners of the casing 30. 48 is mounted on the casing 30. Further, a power switch 54 for starting the radiation detection device 20 and an input terminal 58 for supplying power to the battery 56 in the casing 30 from the outside are disposed on the side portion (frame member 36) of the casing 30. Has been.

  As shown in FIGS. 3 to 5, inside the casing 30, on the base 46 in the first chamber 42, the radiation 12 transmitted through the patient 14 is converted into a radiation image, and the converted radiation image is converted into an electrical signal ( A substantially planar radiation conversion panel 18 that is output as an analog signal) is disposed. On the other hand, in the second chamber 44, a lead plate (shielding member) 62 that absorbs the back scattered radiation of the radiation 12 and prevents the radiation 12 transmitted through the patient 14 from being irradiated to the electronic component 66 and the circuit board 68; A circuit board 68 on which an electronic component 66 that performs amplification processing or the like on the analog signal output from the radiation conversion panel 18 via the flexible board 64 is disposed.

  In this case, the circuit board 68 is disposed through the plurality of cylindrical spacers 70 with respect to the lead plate 62 that is in contact with the bottom surface of the base 46, and the circuit board 68, the spacer 70, and the lead plate 62 are interposed therebetween. By fastening the screw 72 to the base 46, the circuit board 68, the spacer 70, and the lead plate 62 can be fixed to the base 46 in the second chamber 44. Further, a hole 71 for communicating the first chamber 42 and the second chamber 44 is formed on the frame member 36 side of the base 46, and the flexible substrate 64 passes through the hole 71 and the radiation conversion panel. 18 and the electronic component 66 are electrically connected.

  The lead plate 62 may be disposed (attached) on the surface of the base 46 on the first chamber 42 side. Also in this case, the back scattered radiation of the radiation 12 can be absorbed, and irradiation of the radiation 12 to the electronic component 66 and the circuit board 68 can be prevented.

  A heat retaining member 182 that retains the electronic component 66 at or near a predetermined temperature is disposed on the circuit board 68 so as to cover the electronic component 66 and a part of the circuit board 68. That is, the heat retaining member 182 is thermally coupled to the electronic component 66 in the casing 30 without an air layer or the like. The heat retention member 182 is a heat storage member that uses latent heat storage of a material (for example, water) that constitutes the heat retention member 182, and maintains a constant temperature in a temperature region where the phase of the material changes. Accordingly, if the appropriate operating temperature (predetermined temperature, threshold temperature) of the electronic component 66 during the operation of the radiation detection apparatus 20 is set to the constant temperature, the heat retaining member 182 causes the electronic component 66 to move to the operating temperature or the temperature. Heat can be kept near the operating temperature.

  A temperature sensor 180 is disposed on the covering portion of the heat retaining member 182 so as to face the electronic component 66, while a heater 184 is disposed on a portion covering the circuit board 68. . The temperature sensor 180 includes a thermistor or the like, and detects the temperature of the electronic component 66 via the heat retaining member 182. The heater 184 heats the electronic component 66 via the heat retaining member 182. Specifically, the silicon rubber is configured by sandwiching a planar heating element between silicon rubber mixed with glass fiber. Heater, coil heater that generates heat by energizing a spring-like conductor, flat space heater that can heat the surface of the object over a wide range, and high temperature side using the temperature difference between the two sides of the element generated by direct current flow A Peltier device that radiates (heats) heat from the surface can be used.

  4 and 5 illustrate the case where the heat retaining member 182, the temperature sensor 180, and the heater 184 are arranged with respect to one electronic component 66, the other electronic components 66 on the circuit board 68 may be connected to each other. Of course, it is also possible to arrange them. 4 and 5, the temperature sensor 180 is disposed on the heat retaining member 182, but it is needless to say that the temperature sensor 180 may be directly disposed (attached) to the electronic component 66.

The radiation conversion panel 18 includes a scintillator 74 made of a phosphor based on GOS (Gd ₂ O ₂ S: Tb), CsI: Tl, or the like that once converts the radiation 12 transmitted through the patient 14 into visible light, and a thin film transistor (TFT). : Thin Film Transistor) 76 (see FIG. 6) is formed, and the visible light is converted into an electrical signal by using a solid detection element (hereinafter also referred to as a pixel) 78 made of a material such as amorphous silicon (a-Si). It is formed by laminating a photoelectric conversion layer 80 that converts to a layer. The flexible substrate 64 described above electrically connects the TFT 76 of the photoelectric conversion layer 80 and the electronic component 66, and also electrically connects the battery 56 and the pixel 78.

  As shown in FIGS. 3 to 5, in the radiation detection apparatus 20, the first member 34 is connected to the second member 40 via the frame member 36, and the radiation conversion panel 18 is disposed in the first chamber 42. There is no gap between the first member 34 and the base 46, or there is only a slight gap. Therefore, when the casing 30 receives a load from the outside, for example, as shown in FIG. 1, when the patient 14 lies on the casing 30, the load (from the patient 14) is changed from the first member 34 to the frame member 36. Is transmitted to the second member 40 via the first member 34 and to the second member 40 via the radiation conversion panel 18, the base 46 and the frame member 36. It will be a form to receive.

  4 shows the configuration of a so-called back-illuminated radiation conversion panel 18 in which the scintillator 74 and the photoelectric conversion layer 80 are stacked in this order on the base 46. As shown in FIG. The surface irradiation type radiation conversion panel 18 may be configured in such a manner that the photoelectric conversion layer 80 and the scintillator 74 are stacked in this order on the 46.

  Further, as shown in FIG. 3, inside the casing 30, a battery 56 that is a power source of the radiation detection device 20, a cassette control unit 82 that drives and controls the radiation conversion panel 18 by power supplied from the battery 56, A transceiver (wireless communication means) 84 for receiving and transmitting a signal including information (radiation image) of the radiation 12 detected by the radiation conversion panel 18 to and from the console 24 is housed. The cassette controller 82 and the transmitter / receiver 84 are preferably provided with a lead plate or the like on the irradiation surface 32 side of the casing 30 in order to avoid damage due to irradiation with the radiation 12. The battery 56 supplies power to the radiation conversion panel 18, the cassette control unit 82, and the transceiver 84 in the radiation detection apparatus 20.

  In the radiation detection apparatus 20, the battery 56 may be disposed on the second chamber 44 side, or may be driven by receiving power supply from an external power source instead of the battery 56.

  FIG. 6 is a circuit configuration diagram of the radiation detection apparatus 20. The radiation detection apparatus 20 has a structure in which a photoelectric conversion layer 80 in which each pixel 78 made of a substance such as a-Si that converts visible light into an electrical signal is formed is arranged on an array of matrix TFTs 76. In this case, in each pixel 78, the charge generated by converting visible light into an electrical signal (analog signal) is accumulated, and the charge can be read out as an image signal by sequentially turning on the TFT 76 for each row. .

  A gate line 86 extending parallel to the row direction and a signal line 88 extending parallel to the column direction are connected to the TFT 76 connected to each pixel 78. Each gate line 86 is connected to a line scan driver 90, and each signal line 88 is connected to a multiplexer 92. Control signals Von and Voff for controlling on / off of the TFTs 76 arranged in the row direction are supplied from the line scan driving unit 90 to the gate line 86. In this case, the line scan driving unit 90 includes a plurality of switches SW1 for switching the gate lines 86, and an address decoder 94 for outputting a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 82 to the address decoder 94.

  Further, the charge held in each pixel 78 flows out to the signal line 88 through the TFTs 76 arranged in the column direction. This charge is amplified by the amplifier 96. A multiplexer 92 is connected to the amplifier 96 via a sample and hold circuit 98. The multiplexer 92 includes a plurality of switches SW2 that switches the signal line 88 and an address decoder 100 that outputs a selection signal for selecting one of the switches SW2. The address decoder 100 is supplied with an address signal from the cassette control unit 82. An A / D converter 102 is connected to the multiplexer 92, and a radiographic image converted into a digital signal by the A / D converter 102 is supplied to the cassette control unit 82.

  Therefore, in FIG. 6, the line scan driver 90, the multiplexer 92, the amplifier 96, the sample hold circuit 98 and the A / D converter 102 are included in the electronic component 66, while the line scan driver 90 of the gate line 86. A portion from the photoelectric conversion layer 80 to the photoelectric conversion layer 80 and a portion of the signal line 88 from the photoelectric conversion layer 80 to the amplifier 96 are included in the flexible substrate 64.

  Note that the TFT 76 functioning as a switching element may be realized in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to a gate signal referred to as a TFT.

  As shown in FIG. 7, the cassette control unit 82 of the radiation detection apparatus 20 includes an address signal generation unit 104, an image memory 106, a cassette ID memory 108, and a heating control unit 186.

  The address signal generator 104 supplies an address signal to the address decoder 94 of the line scan driver 90 and the address decoder 100 of the multiplexer 92. The image memory 106 stores the radiation image detected by the radiation conversion panel 18. The cassette ID memory 108 stores cassette ID information for specifying the radiation detection apparatus 20.

  The heating control unit 186 constitutes a temperature adjusting unit 190 together with the temperature sensor 180, the heat retaining member 182, and the heater 184.

  The heating control unit 186 executes the program stored in a memory (not shown) during the operation of the radiation detection apparatus 20 by turning on the power switch 54, thereby detecting the temperature (detected temperature) of the electronic component 66 detected by the temperature sensor 180. Based on the comparison with the operating temperature (threshold temperature) or the vicinity of the threshold temperature, the heater 184 is driven to heat the electronic component 66 so that the detected temperature reaches the threshold temperature or the vicinity of the threshold temperature, Alternatively, PID control is performed to keep the electronic component 66 warm so that the detected temperature is held at or near the threshold temperature.

  Specifically, when the radiation detection apparatus 20 is activated by turning on the power switch 54, the heating control unit 186 compares the detected temperature with the threshold temperature or the vicinity of the threshold temperature, and the detected temperature becomes the threshold temperature. Alternatively, if the temperature does not reach the threshold temperature, the heater 184 is driven to heat the electronic component 66, and heating information indicating that the heater 184 is heating is output. In this case, since the heater 184 heats the electronic component 66 via the heat retaining member 182, the heat retaining member 182 is also heated together with the electronic component 66.

  When the detected temperature reaches or near the threshold temperature (or when the detected temperature exceeds the threshold temperature), the heating control unit 186 stops driving the heater 184 and completes heating by the heater 184. The heating completion information (temperature arrival information) indicating that is output. Thereby, the heat retaining member 182 sets the constant temperature of the substance constituting the heat retaining member 182 to the threshold temperature or the vicinity of the threshold temperature, and sets the temperature of the electronic component 66 to the threshold temperature or the vicinity of the threshold temperature. Keep it warm.

  Further, when the detected temperature falls below or near the threshold temperature, the heating control unit 186 drives the heater 184 again so that the detected temperature reaches the threshold temperature or near the threshold temperature. And heating information is output again.

  The transceiver 84 transmits the cassette ID information stored in the cassette ID memory 108 and the radiation image stored in the image memory 106 to the console 24 by wireless communication. Further, the transceiver 84 transmits cassette ID information and heating information or heating completion information to the console 24 by wireless communication.

  The radiographic imaging system 10 and the radiation detection apparatus 20 according to the present embodiment are basically configured as described above, and then operate (temperature control method and radiographic imaging method of the electronic component 66). Will be described with reference to the flowchart of FIG. In this case, the electronic component 66 is heated by the heater 184 so that the temperature of the electronic component 66 reaches the threshold temperature, and then the temperature of the electronic component 66 is maintained at the threshold temperature by the heat retaining member 182. Will be described.

  In step S1, the patient information of the patient 14 to be imaged is registered in advance in the console 24 prior to imaging. If the imaging region and imaging method are determined in advance, these imaging conditions are also registered in advance.

  When taking a radiographic image in an operating room, a medical examination or a round in a hospital, a doctor or a radiographer, for example, places the irradiation surface 32 on the radiation source 16 side at a predetermined position between the patient 14 and the bed. In this state, the radiation detection device 20 is installed.

  In this case, since the patient 14 lies on the irradiation surface 32 of the casing 30, the casing 30 receives a load from the patient 14, but the second member through the frame member 36 from the first member 34. The load is transmitted to the member 40 and the load is transmitted from the first member 34 to the second member 40 via the radiation conversion panel 18, the base 46 and the frame member 36. It will be in the form of receiving. Thereby, the rigidity with respect to the said load from the patient 14 is securable.

  Next, after the power switch 54 is turned on to activate the radiation detection apparatus 20 and the radiation source 16 is appropriately moved to a position facing the radiation detection apparatus 20, the doctor or the radiographer switches the radiographing switch of the radiation source 16. Operate and shoot.

  At that time, when the radiation detection apparatus 20 is activated by turning on the power switch 54, the temperature sensor 180 detects the temperature of the electronic component 66 via the heat retaining member 182 (step S2), and the heating control unit 186 The detected temperature is detected by comparing the temperature detected by the temperature sensor 180 (detected temperature) with the appropriate operating temperature (threshold temperature) of the electronic component 66 during the operation of the radiation detection apparatus 20 by executing the program. Is less than the threshold temperature (step S3).

  When it is determined in step S3 that the detected temperature is lower than the threshold temperature (step S3: YES), the heating control unit 186 drives the heater 184 by PID control, and the heat retaining member 182 is driven from the heater 184. And heating information indicating that the electronic component 66 is being heated is output (step S4).

  The transceiver 84 transmits the cassette ID information and the heating information to the console 24 by wireless communication. By receiving the cassette ID information and the heating information, the console 24 understands that the temperature of the electronic component 66 has not reached the threshold temperature, so that a high-quality radiographic image cannot be obtained even when imaging is performed on the patient 14. can do. Therefore, the console 24 receives the heating information from the radiation detection device 20 even if the radiation source 16 requests the console 24 to transmit imaging conditions by wireless communication due to the operation of the imaging switch. Therefore, the imaging conditions relating to the imaging region of the patient 14 are not transmitted to the radiation source 16.

  Thereafter, the temperature sensor 180 detects the temperature of the electronic component 66 again via the heat retaining member 182 (step S5), and the heating control unit 186 compares the detected temperature with the threshold temperature again, and the detected temperature is detected. It is determined whether or not the temperature is equal to or higher than the threshold temperature (step S6).

  When it is determined in step S6 that the detected temperature is lower than the threshold temperature (step S6: NO), the heating control unit 186 continues driving the heater 184 and performs the process of step S5 again.

  On the other hand, when it is determined in step S6 that the detected temperature is equal to or higher than the threshold temperature (step S6: YES), the detected temperature has reached the threshold temperature, or the detected temperature is the threshold temperature. Therefore, the heating control unit 186 stops driving the heater 184, keeps the electronic component 66 at the threshold temperature by the heat retaining member 182 and confirms that the heating of the electronic component 66 is completed. The heating completion information shown is output (step S7).

  The transceiver 84 transmits the cassette ID information and the heating completion information to the console 24 by wireless communication. The console 24 receives the cassette ID information and the heating completion information, so that the temperature of the electronic component 66 has reached the threshold temperature. Therefore, the console 24 determines that the imaging of the patient 14 is permitted. It can be understood that an image is obtained. Therefore, when there is a request for transmission of imaging conditions by radio communication from the radiation source 16 to the console 24 due to the operation of the imaging switch, the console 24 receives the heating completion information from the radiation detection device 20. Therefore, the imaging condition relating to the imaging region of the patient 14 is transmitted to the radiation source 16 based on the transmission request. When receiving the imaging conditions, the radiation source 16 irradiates the patient 14 with radiation 12 having a predetermined dose according to the imaging conditions (step S8).

  The radiation 12 transmitted through the patient 14 is applied to the radiation conversion panel 18, and the scintillator 74 constituting the radiation conversion panel 18 emits visible light having an intensity corresponding to the intensity of the radiation 12, thereby constituting the photoelectric conversion layer 80. Each pixel 78 that converts visible light into an electrical signal accumulates it as a charge. Next, the charge information, which is the radiation image of the patient 14 held in each pixel 78, is read according to the address signal supplied from the address signal generator 104 constituting the cassette controller 82 to the line scan driver 90 and the multiplexer 92. (Step S9).

  That is, the address decoder 94 of the line scan driver 90 outputs a selection signal according to the address signal supplied from the address signal generator 104, selects one of the switches SW1, and the TFT 76 connected to the corresponding gate line 86. A control signal Von is supplied to the gates of the two. On the other hand, the address decoder 100 of the multiplexer 92 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 104, sequentially switches the switch SW2, and is connected to the gate line 86 selected by the line scan driving unit 90. The radiographic image as the charge information held in each pixel 78 is sequentially read out via the signal line 88.

  The radiation image read out from each pixel 78 connected to the selected gate line 86 is amplified by each amplifier 96, then sampled by each sample hold circuit 98, and then A / D converter via the multiplexer 92. 102, and converted into a digital signal. The radiographic image converted into the digital signal is temporarily stored in the image memory 106 of the cassette control unit 82.

  Similarly, the address decoder 94 of the line scan driving unit 90 sequentially switches the switch SW1 in accordance with the address signal supplied from the address signal generating unit 104, and the charge held in each pixel 78 connected to each gate line 86. A radiation image as information is read out via a signal line 88 and stored in the image memory 106 of the cassette control unit 82 via a multiplexer 92 and an A / D converter 102.

  The radiographic image stored in the image memory 106 is transmitted to the console 24 by wireless communication via the transceiver 84. The console 24 performs predetermined image processing on the received radiographic image (step S10), and stores the radiographic image in association with the registered patient information of the patient 14. The radiographic image subjected to the image processing is transmitted from the console 24 to the display device 22, and the display device 22 displays the radiographic image.

  In step S3 in FIG. 8, if the detected temperature is equal to or higher than the threshold temperature (step S3: NO), it is not necessary to drive the heater 184, so the heating control unit 186 does not perform the processes in steps S4 to S7. To output the heating completion information. The transceiver 84 transmits the cassette ID information and the heating completion information to the console 24 by wireless communication. By receiving the cassette ID information and the heating completion information, the console 24 can grasp that the imaging of the patient 14 is permitted because the temperature of the electronic component 66 has reached the threshold temperature. Thereby, it becomes possible to perform the process after step S8.

  As described above, according to the radiographic imaging system 10 and the radiation detection apparatus 20 according to the present embodiment, the temperature of the electronic component 66 is set to the threshold temperature (appropriate operating temperature of the electronic component 66) or the temperature by the temperature adjusting unit 190. Since the temperature of the electronic component 66 is heated to the vicinity of the threshold temperature and the temperature of the electronic component 66 is maintained at the threshold temperature or the vicinity of the threshold temperature after the heating, the temperature change (temperature increase) of the electronic component 66 after heating is suppressed and the temperature is increased. Both uniform distribution can be realized.

  Therefore, in a state where the temperature change of the electronic component 66 is suppressed and the temperature distribution is made uniform by the temperature adjusting unit 190, the radiation 12 transmitted through the patient 14 is converted into a radiation image by the radiation conversion panel 18, and the radiation conversion panel. If an analog signal of a radiographic image is output from 18 to the electronic component 66, the influence of the temperature change of the electronic component 66 on the analog signal can be reliably reduced, so that a high-quality radiographic image can be easily acquired. It becomes.

  In this case, the temperature adjusting unit 190 is configured by the temperature sensor 180, the heat retaining member 182, the heater 184, and the heating control unit 186, and the heating control unit 186 detects the temperature of the electronic component 66 detected by the temperature sensor 180 (by PID control). When the detected temperature is lower than or near the threshold temperature, the heater 184 is driven. On the other hand, when the detected temperature is equal to or higher than the threshold temperature or near the threshold temperature, the heater 184 is stopped. Therefore, the heating control for the electronic component 66 can be performed efficiently.

  Further, the heat retaining member 182 is disposed in a state of being thermally coupled to the electronic component 66 in the casing 30, the temperature sensor 180 is disposed in the vicinity of the electronic component 66 in the casing 30, and the heater 184 is also disposed in the casing 30. Since it is arranged in the vicinity of the electronic component 66, it is possible to realize both efficient heating control (heating treatment) for the electronic component 66 and efficient heat retention for the heated electronic component 66. Of course, even if the temperature sensor 180 is directly disposed on the electronic component 66, the above-described effects can be easily obtained.

  Further, since the heating information and the heating completion information are transmitted from the radiation detection device 20 to the console 24, the console 24 determines whether or not the heating control for the electronic component 66 is currently performed, or the heat treatment for the electronic component 66 is performed. It can be easily ascertained whether or not imaging for the patient 14 is permitted now. Therefore, when the temperature of the electronic component 66 is held at or near the threshold temperature by the heat retaining member 182 (when the console 24 receives the heating completion information), radiation from the radiation source 16 to the patient 14 is emitted. If the console 24 controls the radiation source 16 so as to irradiate 12, a high-quality radiation image can be reliably acquired. That is, in the present embodiment, acquisition of a low-quality radiation image due to a temperature change of the electronic component 66 can be reliably prevented.

  As described above, in the present embodiment, since the temperature adjustment unit 190 can perform efficient heating control (heating treatment) and heat retention for the electronic component 66, the following effects (1) and (2) are achieved. Can also be obtained.

  (1) The temperature of the electronic component 66 is relatively low. When the radiation detection device 20 is started, the heater 184 is driven, so that the start-up time of the radiation detection device 20 (the temperature of the electronic component 66 is changed from when the power switch 54 is turned on). It is possible to shorten the operating temperature or the time required to reach the vicinity of the operating temperature.

  (2) Reactivation of the radiation detection apparatus 20 by performing heating control or heat retention on the electronic component 66 even when the radiation detection apparatus 20 is in the power saving mode (when power supply from the battery 56 to the radiation conversion panel 18 is stopped). It is also possible to shorten the time (the time from the power saving mode until the radiation detection apparatus 20 shifts to the normal operation).

  In the above description, after the power switch 54 is turned on, the temperature sensor 180 first detects the temperature of the electronic component 66. However, the present embodiment is not limited to the above description. As indicated by the broken line in the flowchart of FIG. 8, the process may proceed to step S4 immediately after the power switch 54 is turned on. In this case, since the processes of steps S2 and S3 are omitted, the effect (1) can be easily obtained.

  In the present embodiment, when the temperature of the electronic component 66 reaches the threshold temperature or near the threshold temperature due to self-heating of the electronic component 66 while the radiation detection apparatus 20 is being driven, the electronic component 66 is moved by the heat retaining member 182. The temperature may be kept at or near the threshold temperature. In this case, since the temperature of the electronic component 66 reaches the threshold temperature or near the threshold temperature due to the self-heating of the electronic component 66, the heater 184 is not necessary, and the configuration of the temperature adjusting unit 190 is simplified. Can do.

  Furthermore, this embodiment can also obtain the following effects by adopting the configuration shown in FIGS.

  In the radiation detection device 20, when the casing 30 receives a load from the outside, the load is transmitted from the irradiation surface 32 to the bottom surface 38 so that the entire casing 30 receives the load. It can be ensured, and the radiation detector 20 can be reduced in weight and thickness.

  In this case, the frame member 36 fixes the periphery of the first member 34 and the periphery of the second member 40, so that the load received by the first member 34 from the outside is interposed via the frame member 36. Can be communicated to.

  Further, a base 46 that divides the inside of the casing 30 into a first chamber 42 and a second chamber 44 is formed inside the frame member 36, and the radiation conversion panel 18 is provided between the first member 34 and the base 46. When the first member 34 receives a load from the outside by being arranged without a gap or by providing a slight gap, the radiation conversion panel 18, the base 46 and the frame member from the first member 34 The load can be transmitted to the second member 40 via 36.

  Therefore, by providing the frame member 36 and the base 46, the load received by the first member 34 from the outside can be reliably transmitted to the second member 40 so that the casing 30 as a whole can receive the load. It is possible to further increase the rigidity against the load.

  Further, the frame member 36 including the base 46 is made of a material having a specific gravity of 2.8 or less, that is, a composite material including carbon fiber, cellulose fiber or glass fiber, aluminum, aluminum alloy, magnesium, magnesium alloy, engineering plastic, and It is composed of any one material among biomass plastics, while the first member 34 and the second member 40 are any of composite materials including carbon fibers, cellulose fibers or glass fibers, engineering plastics and biomass plastics. By comprising only one material, the weight of the radiation detection apparatus 20 as a whole can be reduced. The first member 34 and the second member 40 may be made of the same material or different materials.

  In this case, the first member 34 is composed of a PAN type carbon fiber having a relatively low thermal conductivity, while the second member 40 is composed of a pitch type carbon fiber having a higher thermal conductivity than the PAN type carbon fiber. As a result, it is possible to prevent the patient 14 in contact with the first member 34 from feeling heat due to self-heating of the electronic component 66 and the like, and heat radiation from the second member 40 to the outside is good. It becomes.

  Further, the thickness of the frame member 36 is made thicker than the thickness of the first member 34 and the thickness of the second member 40, while the thickness of the base 46 is made larger than the thickness of the first member 34 and the thickness of the second member 40. Since the rigidity of the frame member 36 and the base 46 can be increased by increasing the thickness, the rigidity of the entire casing 30 with respect to a load from the outside can be further increased.

  Further, the casing 30 has an octagonal shape with the corners cut off in plan view, and the shock absorbing member 48 is attached to each of the cut off corners. The absorbing member 48 can reliably absorb the material.

  Furthermore, in this embodiment, the scintillator 74 and the photoelectric conversion layer 80 are stacked in this order on the base 46, or the photoelectric conversion layer 80 and the scintillator 74 are stacked in this order. Light can be efficiently converted into an electrical signal (analog signal) by the photoelectric conversion layer 80. As a result, a high-quality radiation image can be obtained.

  Further, in the present embodiment, signals are transmitted and received by radio communication between the console 24 and the radiation detection device 20, the radiation source 16, and the display device 22, so a cable for transmitting and receiving signals becomes unnecessary. There is no risk of disturbing the work of the doctor or radiologist. Therefore, the doctor or radiologist can perform his / her work efficiently.

  Furthermore, in this embodiment, a radiographic image is taken due to the operation of the radiographic source 16 imaging switch by the doctor or radiographer, but the radiographic image is taken due to the operation of the console 24 by the doctor or radiographer. May be performed.

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

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

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

  Further, the wireless communication between the radiation detection apparatus 20 and the external device may be performed by optical wireless communication using infrared rays or the like instead of normal communication using radio waves.

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

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

  As shown in FIG. 9, the first modification is different from the embodiment of FIGS. 1 to 8 in that the heating control unit 186 is in the console 24.

  In this case, when the power switch 54 is turned on, a signal indicating that the power switch 54 has been turned on is transmitted from the transceiver 84 to the heating control unit 186 of the console 24 via wireless communication. Further, the temperature (detected temperature) of the electronic component 66 is transmitted from the temperature sensor 180 to the heating control unit 186 in the console 24 by wireless communication via the transceiver 84. Further, the heater 184 is driven and controlled by the heating control unit 186 via the transceiver 84 by wireless communication. Thereby, it is also possible to perform heating control on the electronic component 66 from the console 24 side.

  As shown in FIG. 10, the second modification is different from the embodiment of FIGS. 1 to 8 in that heating control and heat retention are performed on the electronic component 66 when the radiation detection apparatus 20 is loaded into the cradle 200.

  The cradle 200 has a substantially U-shape when viewed from the side, and the radiation detection device 20 is loaded in the recess of the cradle 200 with the battery 56 on the lower side. In this case, only the temperature sensor 180 facing the electronic component 66 is disposed on the heat retaining member 182. On the other hand, the cradle 200 includes a charge processing unit 202 that charges the battery 56 via an input terminal 58 (see FIG. 2), a display unit 204, and a transceiver 206 that can transmit and receive to the outside. A heater 184 and a heating control unit 186 are also provided.

  The heater 184 is disposed in the cradle 200 at a position close to the electronic component 66, specifically, on the side of the cradle 200 that faces the electronic component 66. Further, the temperature (detected temperature) of the electronic component 66 detected by the temperature sensor 180 is transmitted from the transceiver 84 (see FIG. 3) of the radiation detection apparatus 20 to the transceiver 206 by wireless communication.

  Thereby, the transceiver 206 outputs the detected temperature received from the transceiver 84 to the heating control unit 186, and the heating control unit 186 determines whether the detected temperature input from the transceiver 206 and the threshold temperature or the vicinity of the threshold temperature. Based on the comparison, the heater 184 can be driven or stopped. The heater 184 heats the electronic component 66 through the second member 40, the air layer in the casing 30 (second chamber 44 in FIGS. 4 and 5), and the heat retaining member 182.

  The display unit 204 can display the charging state of the radiation detection device 20 based on the signal from the charging processing unit 202. In addition, the display unit 204 is currently performing heating control on the electronic component 66 based on heating information or heating completion information from the heating control unit 186, or currently performing heat treatment on the electronic component 66. Can be displayed. Furthermore, the display unit 204 can use the radiation detection device 20 loaded in the cradle 200 based on a signal indicating completion of charging from the charging processing unit 202 and heating completion information from the heating control unit 186. Can also be displayed. Needless to say, the display unit 204 may display necessary information including a radiation image acquired from the radiation detection apparatus 20.

  As described above, in the second modified example, charging of the battery 56 and heating control for the electronic component 66 using the heater 184 disposed outside the casing 30 with the radiation detection device 20 loaded in the cradle 200, or Since the heat treatment for the electronic component 66 can be performed at the same time, the charging process and the heating control or the heat treatment can be performed efficiently.

  The cradle 200 may be disposed at a necessary location in the operating room or hospital, and not only charging the battery 56 but also using the wireless communication function or the wired communication function of the transceiver 206, the RIS 26, the HIS 28, the console. Necessary information may be exchanged with an external device such as 24. The information to be transmitted / received can include a radiographic image recorded in the radiation detection device 20 loaded in the cradle 200.

  Further, a plurality of cradles 200 are connected to a network, and the charging state and heating completion information of the radiation detection devices 20 loaded in each cradle 200 are collected via the network, and the radiation detection devices 20 in a usable state are collected. It can also be configured to confirm the location.

  As shown in FIG. 11, when the battery 56 in the radiation detection apparatus 20 is charged from the cradle 200 via the cable 208, the third modified example has a heater 184 connected to the connector 210 of the cable 208 connected to the input terminal 58. Is different from the second modification (see FIG. 10) in that it is built in. In FIG. 11, the configuration of the battery 56, the cassette control unit 82, and the transmitter / receiver 84 in the casing 30 is illustrated in the form of a plan view and a broken sectional view, but for ease of explanation, radiation conversion is performed. Illustration of the panel 18, the base 46, the lead plate 62, the flexible substrate 64, etc. is omitted.

  In this case, when the connector 210 and the input terminal 58 are connected, the cradle 200 charges the battery 56 via the cable 208, the connector 210, the input terminal 58, and the cable 212 in the casing 30.

  As in the case of the second modification, the transceiver 84 transmits the temperature (detected temperature) of the electronic component 66 detected by the temperature sensor 180 to the transceiver 206 by wireless communication, and the transceiver 206 is The detected temperature received from 84 is output to the heating control unit 186. The heating control unit 186 drives or stops the heater 184 in the connector 210 via the cable 208 based on the comparison between the detected temperature input from the transceiver 206 and the threshold temperature or the vicinity of the threshold temperature. Thereby, the heater 184 can heat the electronic component 66 via the frame member 36, the air layer in the casing 30, and the heat retaining member 182.

  Also in the third modified example, since the heating control for the electronic component 66 can be performed by the heater 184 outside the casing 30, the same effect as the second modified example can be obtained.

  As shown in FIGS. 12 and 13, the fourth modification and the fifth modification are shown in FIG. 1 to FIG. 1 in that handle parts 140 and 152 are provided on the side part (frame member 36) of the casing 30, respectively. This is different from the eighth embodiment.

  In this case, by providing the radiation detection device 20 with the handle portions 140 and 152, the radiation detection device 20 can be easily handled and carried.

  In the radiation detection apparatus 20, a guide line 142 serving as a reference for the imaging region and the imaging position is formed on the irradiation surface 32 side. By using the guide line 142 to position the patient 14 with respect to the radiation detection apparatus 20 and setting the irradiation range of the radiation 12, a radiation image can be recorded in an appropriate imaging region.

  A display unit 144 that displays various types of information related to the radiation detection apparatus 20 is disposed at a site outside the imaging region of the radiation detection apparatus 20. The display unit 144 includes the ID information of the patient 14 recorded in the radiation detection device 20, the number of times the radiation detection device 20 is used, the cumulative exposure dose, and the state of charge of the battery 56 built in the radiation detection device 20 (remaining amount). Capacity), radiographic image capturing conditions, positioning image of the patient 14 with respect to the radiation detection apparatus 20, and the like are displayed. In this case, for example, the radiologist confirms the patient 14 according to the ID information displayed on the display unit 144 and confirms in advance that the radiation detection device 20 is in a usable state, and the displayed positioning image. The desired radiographic image of the patient 14 can be positioned on the radiation detection device 20 based on the above, and an optimal radiographic image can be captured.

  The frame member 36 is preferably provided with a USB (Universal Serial Bus) terminal 146 and a card slot 148 into which the memory card 150 is loaded.

  The USB terminal 146 or the card slot 148 can be used when the radiation detection apparatus 20 cannot transmit and receive information by wireless communication with an external device such as the console 24. That is, by connecting a cable to the USB terminal 146, information can be transmitted / received to / from an external device by wired communication. In addition, information can be transmitted and received by loading the memory card 150 into the card slot 148 and recording necessary information on the memory card 150 and then removing the memory card 150 and loading it into an external device.

  The input terminal 58 is connected to an AC adapter when the charging function of the battery 56 built in the radiation detection apparatus 20 is deteriorated or when sufficient time cannot be secured for charging the battery 56. By supplying electric power from the above, the radiation detection apparatus 20 can be immediately put into a usable state.

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

DESCRIPTION OF SYMBOLS 10 ... Radiation imaging system 12 ... Radiation 14 ... Patient 16 ... Radiation source 18 ... Radiation conversion panel 20 ... Radiation detection apparatus 22 ... Display apparatus 24 ... Console 30 ... Casing 34 ... 1st member 36 ... Frame member 40 ... 2nd member 56 ... Battery 66 ... Electronic component 68 ... Circuit board 84 ... Transmitter / receiver 180 ... Temperature sensor 182 ... Heat retaining member 184 ... Heater 186 ... Heating controller 190 ... Temperature adjusting means 200 ... Cradle 210 ... Connector

Claims (21)

A housing made of a material that transmits radiation, a radiation conversion panel that is housed in the housing and converts the radiation transmitted through the subject into a radiation image, and is housed in the housing and output from the radiation conversion panel A radiation detection apparatus comprising an electronic component for processing the radiation image;
Temperature adjusting means for holding the temperature of the electronic component that has reached a predetermined temperature or in the vicinity of the predetermined temperature at the predetermined temperature or in the vicinity of the predetermined temperature;
A radiographic imaging system comprising: The system of claim 1, wherein
The temperature adjusting means holds the temperature of the electronic component that has reached or near the predetermined temperature due to self-heating of the electronic component, or heats the electronic component. The radiographic imaging system characterized in that the temperature of the electronic component that has reached the predetermined temperature or near the predetermined temperature is maintained at or near the predetermined temperature. The system of claim 2, wherein
The temperature adjusting means is
A temperature sensor for detecting a temperature of the electronic component or a temperature in the vicinity of the electronic component;
A heat retaining member for maintaining the temperature of the electronic component at or near the predetermined temperature;
A radiographic imaging system comprising: The system of claim 3, wherein
The temperature adjusting means is
A heater for heating the electronic component so that the temperature of the electronic component rises to the predetermined temperature or near the predetermined temperature;
The temperature of the electronic component detected by the temperature sensor or a temperature in the vicinity of the electronic component is compared with the predetermined temperature or in the vicinity of the predetermined temperature, and the temperature of the electronic component reaches the predetermined temperature or in the vicinity of the predetermined temperature. A heating control unit for controlling the heater,
Further comprising
The heat retention member holds the temperature of the electronic component at the predetermined temperature or in the vicinity of the predetermined temperature after the electronic component is heated by the heater. The system of claim 4, wherein
The heating control unit drives the heater when the temperature of the electronic component falls below the predetermined temperature or near the predetermined temperature, while the temperature of the electronic component exceeds the predetermined temperature or near the predetermined temperature. In this case, the radiation image capturing system is characterized in that the driving of the heater is stopped. The system according to claim 4 or 5,
The casing is provided with a switch for activating the radiation detection apparatus,
When the switch is turned on and the radiation detection apparatus is activated, the heating control unit drives the heater to heat the electronic component. The system of claim 6, wherein
The heating control unit stops driving of the heater when the temperature of the electronic component exceeds the predetermined temperature or in the vicinity of the predetermined temperature. The system according to any one of claims 4 to 7,
The heating control unit controls the temperature of the electronic component by PID control. The system according to any one of claims 4 to 8,
The temperature sensor is arranged in the vicinity of the electronic component in the housing,
The heat retaining member is disposed in the housing and thermally coupled to the electronic component,
The radiographic imaging system, wherein the heating control unit and the heater are disposed inside or outside the casing. The system of claim 9, wherein
A control device for controlling the radiation detection device;
The heating control unit is provided in the control device,
The radiation image capturing system according to claim 1, wherein the heater is disposed in the housing and is thermally coupled to the electronic component. The system of claim 9, wherein
The radiation detection apparatus further includes a battery that drives the radiation conversion panel,
The radiographic image capturing system further includes a cradle that charges the battery and a control device that controls the radiation detection device. The system of claim 11, wherein
The heating control unit and the heater are provided in the cradle,
The radiographic imaging system, wherein the heater can heat the electronic component when the radiation detection apparatus is loaded in the cradle. The system of claim 11, wherein
A cable connecting the cradle and the battery;
The heating control unit is provided in the cradle,
The heater is provided in a connector on the battery side of the cable,
The radiographic imaging system, wherein the heater can heat the electronic component when the cradle is electrically connected to the battery via the cable and the connector. The system according to any one of claims 9 to 13,
A radiation source for outputting the radiation;
The control device controls the radiation source and the radiation detection device;
The radiation detection apparatus transmits the radiation image converted by the radiation conversion panel to the control device. The system of claim 14, wherein
When the temperature of the electronic component reaches the predetermined temperature or the vicinity of the predetermined temperature, the temperature adjusting means includes temperature arrival information indicating that the temperature of the electronic component reaches the predetermined temperature or the vicinity of the predetermined temperature. Output to the control unit,
The said control apparatus controls the said radiation source based on the said temperature arrival information input, and outputs the said radiation from this radiation source, The radiographic imaging system characterized by the above-mentioned. The system according to any one of claims 1 to 15,
The radiation conversion panel includes a scintillator that converts the radiation into visible light, a solid state detection element that converts the visible light into an electrical signal, and a reading unit that reads the electrical signal from the solid state detection element as the radiation image. A radiographic imaging system characterized by that. A housing made of a material that transmits radiation;
A radiation conversion panel that is housed in the housing and converts the radiation transmitted through the subject into a radiation image;
An electronic component housed in the housing and for processing the radiation image output from the radiation conversion panel;
Temperature adjusting means for holding the temperature of the electronic component that has reached a predetermined temperature or in the vicinity of the predetermined temperature at the predetermined temperature or in the vicinity of the predetermined temperature;
A radiation detection apparatus comprising: The apparatus of claim 17.
When the temperature of the electronic component reaches the predetermined temperature or in the vicinity of the predetermined temperature, the temperature adjusting means externally displays temperature arrival information indicating that the temperature of the electronic component reaches the predetermined temperature or in the vicinity of the predetermined temperature. The radiation detection apparatus is characterized in that imaging of the subject by the output of the radiation from a radiation source is permitted. The radiation transmitted through the subject is converted into a radiation image by a radiation conversion panel housed in a housing made of a material that transmits radiation, and the radiation image output from the radiation conversion panel is converted by an electronic component in the housing. When processing
A program to be executed by a temperature adjusting means for controlling the temperature of the electronic component,
A program for maintaining a temperature of the electronic component that has reached a predetermined temperature or near the predetermined temperature at or near the predetermined temperature. The radiation transmitted through the subject is converted into a radiation image by a radiation conversion panel housed in a housing made of a material that transmits radiation, and the radiation image output from the radiation conversion panel is converted by an electronic component in the housing. When processing
A temperature control method for an electronic component, wherein the temperature of the electronic component that has reached a predetermined temperature or near the predetermined temperature is held by the temperature adjusting means at or near the predetermined temperature.   21. The imaging of the subject is performed by outputting the radiation from a radiation source when the temperature of the electronic component is held at or near the predetermined temperature by the temperature control method according to claim 20. A radiographic imaging method.

Images