JP2010085266A - Radiation detecting device and radiography system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To improve the waterproofness, moistureproofness and impact resistance of a flexible radiation detector and thereby to enhance the reliability of a radiation detecting device. <P>SOLUTION: The radiation detecting device 18 includes a grid 38 which removes scattered radiation of radiation 12 caused by a subject 14, a sensor board 40 which constitutes the radiation detector 30 detecting the radiation 12 transmitted through the subject 14, a lead sheet 42 which absorbs back scattered radiation of the radiation 12, and a sealing protective film 44 which is formed at a heating temperature of 150°C or below so that it covers the grid 38, the sensor board 40 and the lead sheet 42, and consists of a material transmitting the radiation 12. The device has flexibility as a whole. At least the surface base material of the sealing protective film 44 is colored with black and the film has a light shielding property. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a radiation detection apparatus including a radiation detector that detects radiation transmitted through a subject and converts the detected radiation into radiation image information, and a radiation imaging system including the radiation detection apparatus.

  In the medical field, radiation imaging systems that irradiate a subject with radiation and guide the radiation transmitted through the subject to a radiation detector to capture radiation image information are widely used. As the radiation detector, a conventional radiation film in which the radiation image information is exposed and recorded, or radiation energy as the radiation image information is accumulated in a phosphor, and the radiation image information is obtained by irradiating excitation light. A stimulable phosphor panel that can be extracted as stimulated emission light is known. These radiation detectors supply the radiation film on which the radiation image information is recorded to a developing device to perform development processing, or supply the storage phosphor panel to a 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 radiation image information from a radiation detector after imaging in order to perform a quick and accurate treatment on a patient. Radiation detection using a solid state detector that converts radiation directly into an electrical signal, or converts radiation into visible light with a scintillator, and then converts it into an electrical signal and reads it out A vessel has been developed.

  Regarding a radiation detection apparatus that houses a radiation detector, Patent Document 1 proposes to arrange a flexible radiation detector in accordance with the surface shape of a patient.

  Patent Document 2 discloses an example in which a sensor panel and a scintillator panel are sealed with a protective resin layer at a position facing the housing, and a sensor resin layer and a scintillator panel that are formed vertically. A sealed example has been proposed.

JP 2003-70776 A JP 2006-337184 A

  However, the radiation detection apparatus described in Patent Document 1 simply houses a flexible radiation detector in a flexible case, and protects the scintillator inside the radiation detector, for example, There is no mention of waterproofing or moisture proofing for the scintillator.

  The radiation detection apparatus described in Patent Document 2 has a configuration in which a rigid sensor panel and a scintillator panel are hermetically sealed with a protective resin layer. Therefore, no consideration is given to a radiation detector having flexibility. Not.

  The present invention has been made in view of the above-described problems, and can improve the waterproofness, moistureproofness, and impact resistance of a flexible radiation detector, and the reliability of the radiation detection apparatus and the radiation imaging system. An object of the present invention is to provide a radiation detection apparatus and a radiation imaging system that can improve the image quality.

  A radiation detection apparatus according to a first aspect of the present invention detects radiation transmitted through a subject and converts it into radiation image information, and has a flexible radiation detector, and at least a part or all of the radiation detector. And a sealing protective film made of a material that transmits the radiation.

  A radiation imaging system according to the second aspect of the invention includes the above-described radiation detection apparatus according to the first aspect of the invention, a radiation source that outputs the radiation, and a control device that controls the radiation source and the radiation detection apparatus. It is characterized by having.

  As described above, according to the radiation detection apparatus and the radiation imaging system of the present invention, the waterproofness, moisture resistance, and impact resistance of the flexible radiation detector can be improved, and the reliability of the radiation detection apparatus can be improved. Can increase the sex. Moreover, it can be sterilized and washed as necessary, and one radiation detection device can be used repeatedly. This also leads to lower running costs.

  Embodiments of the radiation detection apparatus and the radiation imaging system according to the present invention will be described below with reference to FIGS.

  First, as shown in FIG. 1, a radiation imaging system 10 according to the present exemplary embodiment includes a radiation source 16 for irradiating a subject (for example, a patient 14) with radiation 12 having a dose according to imaging conditions, and the present embodiment. , A display device 20 that displays radiation image information based on the radiation 12 detected by the radiation detection device 18, a console that controls the radiation detection device 18, the radiation source 16, and the display device 20. 22 (control device). Between the console 22 and the radiation detection device 18, the radiation source 16, and the display device 20, for example, UWB (Ultra Wide Band), IEEE 802.11. Signals are transmitted and received by wireless communication using a wireless LAN such as a / g / n or millimeter waves. The console 22 is connected to a radiology information system (RIS) 24 that comprehensively manages radiographic image information and other information handled in the radiology department in the hospital, and the RIS 24 is connected to medical information in the hospital. A medical information system (HIS) 26 for comprehensively managing information is connected.

  The radiation detection apparatus 18 according to the present embodiment includes a flexible radiation detector 30 (see FIG. 2) that detects the radiation 12 that has passed through the subject 14 and converts the radiation 12 into radiation image information, and a power source for the radiation detector 30. A signal including information on the radiation 12 detected by the radiation detector 30 and the console 22 are transmitted and received between the battery 32, the control unit 34 that drives and controls the radiation detector 30 by the power supplied from the battery 32, and the console 22. A transceiver 36 (wireless communication means) is accommodated. The battery 32 supplies power to the radiation detector 30, the control unit 34, and the transceiver 36.

  In addition, as shown in FIG. 3, the radiation detection device 18 includes a grid 38 that removes scattered rays of the radiation 12 caused by the subject 14 and a sensor substrate that constitutes a radiation detector 30 that detects the radiation 12 transmitted through the subject 14. 40 and a lead sheet 42 that absorbs backscattered rays of the radiation 12, and the grid 38, the sensor substrate 40, and the lead sheet 42 are sequentially arranged with respect to the irradiation surface (imaging surface) 30a on the subject 14 side. Is done. The grid 38, sensor substrate 40, and lead sheet 42 are also flexible. Further, the irradiation surface 30 a may be configured as the grid 38.

  As shown in FIGS. 3 and 4, the radiation detection device 18 has a sealing protective film 44 made of a material that covers at least a part or the whole of the radiation detector 30 and transmits the radiation 12. And it has flexibility as a whole. Further, the sealing protective film 44 has a light shielding property because at least the front substrate is colored black. 3 and 4, a sealing protective film 44 is formed so as to cover the grid 38, the sensor substrate 40, and the lead sheet 42. Here, “sealing” refers to a case where a part of the radiation detector 30 is covered in order to improve the waterproofness, moisture resistance, and impact resistance of the radiation detector 30 having flexibility, or radiation detection. Including sealing, or “sealing,” the entire vessel 30.

  Accordingly, when the subject 14 is not irradiated with the radiation 12 (non-imaging), it is wound up in a roll shape and can be stored in a storage box (not shown). When the subject 14 is irradiated with the radiation 12 (at the time of imaging), as shown in FIG.

  As shown in FIG. 4, the sensor substrate 40 includes a flexible base 71, and a TFT layer in which a scintillator 72 and an array of thin film transistors (TFTs) are formed on the flexible base 71. 74 and the photoelectric conversion layer 76 are laminated in this order.

The scintillator 72 is made of a phosphor such as GOS (Gd ₂ O ₂ S) or CsI that once converts the radiation 12 (see FIG. 1) transmitted through the subject 14 into visible light. The TFT layer 74 is formed with an array of thin film transistors (TFT 52: see FIG. 6), and can transmit the radiation 12 and visible light. The photoelectric conversion layer 76 converts the visible light into an electrical signal using a solid detection element (hereinafter also referred to as the pixel 50) made of a substance such as amorphous silicon (a-Si).

  As a constituent material of the flexible substrate 71, for example, as shown in Patent Document 1, polyethylene terephthalate (PET), polyethylene naphthalate (PEN), polyimide (for example, Kapton (registered trademark) of DuPont), polysulfone ether (PES), polycarbonate and the like can be used.

  In addition, as shown in FIG. 3, a circuit board 78 is disposed around the sensor board 40 along the side portion of the sensor board 40, and the driving circuit IC of the radiation detector 30 is arranged on the circuit board 78. A (driving unit) 80a and a reading circuit IC (reading unit) 80b are arranged. The driving circuit IC 80a drives the TFT 52 of the sensor substrate 40, and the reading circuit IC 80b reads out the electric charge accumulated in the pixel 50 as an image signal based on the driving of the TFT 52 by the driving circuit IC 80a.

  Furthermore, on the circuit board 78, a battery 32 that is a power source of the radiation detection device 18, a control unit 34 that drives and controls the radiation detector 30 with power supplied from the battery 32, and radiation detected by the radiation detector 30. A transceiver 36 that transmits and receives signals including 12 pieces of information to and from the console 22 is disposed. Accordingly, the battery 32 supplies power to the radiation detector 30, the control unit 34, and the transceiver 36 in the radiation detection apparatus 18. In addition, in order to avoid the damage by the radiation 12 being irradiated to the control part 34 and the transmitter / receiver 36, it is preferable to arrange | position a lead board etc. to the irradiation surface 30a side.

  As shown in FIG. 6, the radiation detector 30 includes a matrix array of TFTs 52 (TFTs) in which each pixel 50 made of a substance such as a-Si that converts visible light into an electrical signal is formed. Having a structure disposed on layer 74). In this case, in each pixel 50, electric charges generated by converting visible light into electric signals are accumulated, and the electric charges can be read out as image signals by sequentially turning on the TFTs 52 for each row.

  A gate line 54 extending parallel to the row direction and a signal line 56 extending parallel to the column direction are connected to the TFT 52 connected to each pixel 50. Each gate line 54 is connected to a line scan driving unit 58 including a plurality of driving circuit ICs 80 a, and each signal line 56 is connected to a multiplexer 66. Control signals Von and Voff for controlling on / off of the TFTs 52 arranged in the row direction are supplied from the line scanning drive unit 58 to the gate line 54. In this case, the line scan driving unit 58 includes a plurality of switches SW1 that switches the gate lines 54, and an address decoder 60 that outputs a selection signal for selecting one of the switches SW1. An address signal is supplied from the control unit 34 to the address decoder 60.

  In addition, the charge held in each pixel 50 flows out to the signal line 56 through the TFTs 52 arranged in the column direction. This charge is amplified by the amplifier 62. A multiplexer 66 is connected to the amplifier 62 via a sample and hold circuit 64. The multiplexer 66 includes a plurality of switches SW2 for switching the signal line 56, and an address decoder 68 for outputting a selection signal for selecting one of the switches SW2. An address signal is supplied from the control unit 34 to the address decoder 68. An A / D converter 70 is connected to the multiplexer 66, and radiation image information converted into a digital signal by the A / D converter 70 is supplied to the control unit 34. The amplifier 62, the sample hold circuit 64, the multiplexer 66, and the A / D converter 70 constitute a read circuit unit 69 including a plurality of read circuit ICs 80b.

  Further, as shown in FIG. 1, the control unit 34 of the radiation detection apparatus 18 includes an address signal generation unit 82, an image memory 84, and an ID memory 86.

  The address signal generator 82 supplies an address signal to the address decoder 60 of the line scan driver 58 and the address decoder 68 of the multiplexer 66 that constitute the radiation detector 30. The image memory 84 stores the radiation image information detected by the radiation detector 30. The ID memory 86 stores ID information for specifying the radiation detection device 18.

  The transceiver 36 transmits the ID information stored in the ID memory 86 and the radiation image information stored in the image memory 84 to the console 22 by wireless communication.

  On the other hand, for example, a method of forming the sealing protective film 44 by laminating a thin sheet material (film) is preferably employed. In this case, the sealing protective film 44 is formed by a hot laminating method or a cold laminating method. Examples of the hot laminating method include an extrusion laminating method, a dry laminating method, a non-solvent laminating method, and a heat laminating method. Examples of the cold laminating method include an extrusion laminating method and a dry laminating method.

  In the extrusion laminating method, various polymer films, paper, aluminum foil or a laminated film thereof is used as a base material, and an organic titanate-based, butadiene-based, isocyanate-based anchor coating agent is applied. And it is the method of melt-bonding the polyolefin resin etc. to a base material while extruding into a film from an extruder and T-die.

  The dry laminating method uses an isocyanate-based adhesive diluted with a solvent, applies the above-mentioned adhesive to various polymer films, paper, aluminum foil or laminated films thereof, and removes the solvent by drying. . And while an adhesive agent has adhesive force, it is the method of superposing | stacking another polymer film, paper, aluminum foil, or these laminated films, and pressure-bonding together.

  In the non-solvent laminating method, a solventless adhesive such as an isocyanate is heated at 80 to 100 ° C. and applied to various polymer films, paper, aluminum foil, or a laminated film thereof in a state where the viscosity is lowered. And after apply | coating, it is the method of pressure-bonding this and another polymer film, paper, aluminum foil, or these laminated films with a heating roll.

  In the heat laminating method, polymer films to be bonded to each other or a metal plate such as tin-free steel and a polymer film are pressed with a heating roll, and one or both of the films to be bonded are melted and thermally bonded to integrate them. It is a method to do.

  When the hot laminating method is used, it is preferable to use a laminate film that can be formed at a heating temperature of 180 ° C. or lower, preferably 150 ° C. or lower.

  The laminate film is a laminate in which at least a front substrate, an intermediate substrate, a coat layer, and a sealant layer are laminated in this order. When the laminate film is coated on at least the radiation detector 30, the outer surface substrate, A sealant layer is located inside.

  Examples of the surface base material include polyester films such as polyethylene terephthalate and polybutylene terephthalate, polyamide films such as nylon 6, nylon 6,6, polymetaxylylene adipamide (N-MXD6), low density polyethylene, and high density. Polyolefin film such as polyethylene, linear low density polyethylene, polypropylene, polyacrylonitrile film, poly (meth) acrylic film, polystyrene film, polycarbonate film, ethylene-vinyl alcohol copolymer (EVOH) film, polyvinyl Polyvinylidene chloride (PVDC) resin, polyvinyl alcohol resin, ethyl alcohol film, paper such as carton, metal foil such as aluminum and copper, and various materials used as these substrates Disperse film coated with various polymers such as saponified vinyl resin, acrylic resin, deposited metal such as aluminum, dispersed fine metal powder, inorganic filler, etc. And a film provided with an oxygen scavenging function can be used. Moreover, an inorganic filler can be disperse | distributed also about the various polymers to coat. Examples of inorganic fillers include silica, alumina, mica, talc, aluminum flakes, glass flakes, etc., but layered silicates such as montmorillonite are preferred, and dispersion methods thereof include, for example, extrusion kneading and resin solutions. A conventionally known method such as a mixed dispersion method can be used. Examples of methods for imparting oxygen scavenging functions include hindered phenols, vitamin C, vitamin E, organic phosphorus compounds, gallic acid, pyrogallol and other low molecular organic compounds that react with oxygen, cobalt, manganese, nickel, iron And a method of using a composition containing a transition metal compound such as copper at least in part.

  The thickness of these film materials is about 10 to 300 μm, preferably about 10 to 100 μm, and in the case of a plastic film, the film material may be uniaxially or biaxially stretched.

  The intermediate base material includes a silica vapor deposition layer or an alumina vapor deposition layer, and is formed by vapor-depositing silica or alumina on the surface base material described above. The method for vapor deposition on the front substrate may be physical vapor deposition or chemical vapor deposition. The silica vapor deposition layer or the alumina vapor deposition layer may be one in which silica and alumina are vapor-deposited.

  Examples of the resin used as the coating layer include polyurethane resins such as polyurethane resins, polyurethane urea resins, acrylic modified urethane resins and acrylic modified urethane urea resins; vinyl chloride-vinyl acetate copolymer resins; rosins such as rosin modified maleic resins. Polyamide resins; Polyester resins; Chlorinated olefin resins such as chlorinated polypropylene resins, polyethyleneimine resins, polybutadiene resins, and organic titanium resins. A coating layer can be formed by dissolving these resins in a solvent such as water, methanol, ethanol, 2-propanol, ethyl acetate, methyl ethyl ketone, and toluene and applying the resin by a gravure method, a roll coating method, or the like. For the formation of the coating layer, general printing equipment that has been used for printing on a conventional polymer film such as a gravure printing machine, a flexographic printing machine, and an offset printing machine can be similarly applied.

  The practical thickness of the coat layer is 0.005 to 5 μm, preferably 0.01 to 3 μm. When the thickness is less than 0.005 μm, sufficient adhesion is hardly exerted. On the other hand, when the thickness exceeds 5 μm, it is difficult to form a resin layer having a uniform thickness.

  When a curable coating layer is used, it may be a one-component type or a two-component type. However, when it is desired to impart water resistance and heat resistance, it is more practical to use a two-component type.

  In addition, an additive may be included in the above resins in order to impart other functionality to the coat layer. For example, wax, dispersant, antistatic agent, surface modifier and the like can be used for improving friction resistance, blocking prevention, slipping, heat resistance, antistatic, etc., which can be appropriately selected and used. .

  As the sealant layer, it is preferable to use a flexible polymer film. Considering the expression of good heat sealability, a polyolefin film such as a polyethylene film, a polypropylene film, or an ethylene-vinyl acetate copolymer should be selected. Is preferred. The thickness of these films is practically about 10 to 300 μm, preferably about 10 to 100 μm, and various surface treatments such as flame treatment and corona discharge treatment may be performed on the surface of the film.

  The radiation detection apparatus 18 and the radiation imaging system 10 according to the present embodiment are basically configured as described above, and the operation thereof will be described next.

  Patient information of the patient 14 to be imaged is registered in advance in the console 22 prior to imaging. If the imaging region and imaging method are determined in advance, these imaging conditions are also registered in advance.

  When radiographic image information is taken in an operating room, medical examination or in a hospital round, a doctor or a radiographer takes out a roll-shaped radiation detection device 18 from a storage box (not shown), for example, the patient 14 and a bed The radiation detection apparatus 18 is installed at a predetermined position between the irradiation surface 30a and the irradiation surface 30a on the radiation source 16 side. At this time, since the sealing protective film 44 has a light shielding property, external light (light from a fluorescent lamp or the like) is blocked from entering the radiation detector 30, and generation of unnecessary charges due to external light can be reduced. it can.

  Next, the doctor or radiologist turns on the power switch of the radiation detection device 18. Thereby, power supply from the battery 32 to the radiation detector 30, the control unit 34, and the transceiver 36 is started, and the drive circuit IC 80a, the readout circuit IC 80b, the control unit 34, and the transceiver 36 start operation.

  Then, after appropriately moving the radiation source 16 to a position facing the radiation detection device 18, the doctor or the radiographer operates the imaging switch of the radiation source 16 to perform imaging. Based on the operation of the imaging switch, the radiation source 16 requests transmission of imaging conditions to the console 22 by wireless communication, and the console 22 relates to the imaging region of the patient 14 based on the received request. The imaging conditions are transmitted to the radiation source 16. 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.

  The radiation 12 transmitted through the patient 14 passes through the sealing protective film 44 of the radiation detection device 18, and after the scattered radiation is removed by the grid 38, the radiation detector 30 is irradiated. The scintillator 72 of the radiation detector 30 emits visible light having an intensity corresponding to the intensity of the radiation 12, and each pixel 50 constituting the photoelectric conversion layer 76 converts the visible light into an electric signal and accumulates it as an electric charge. Next, the charge information which is the radiation image information of the patient 14 held in each pixel 50 is read according to the address signal supplied from the address signal generation unit 82 of the control unit 34 to the line scanning drive unit 58 and the multiplexer 66.

  That is, the address decoder 60 of the line scan driver 58 outputs a selection signal according to the address signal supplied from the address signal generator 82 to select one of the switches SW1, and the TFT 52 connected to the corresponding gate line 54. A control signal Von is supplied to the gates of the first and second gates. On the other hand, the address decoder 68 of the multiplexer 66 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 82, sequentially switches the switch SW2, and is connected to the gate line 54 selected by the line scan driving unit 58. Radiation image information that is charge information held in each pixel 50 is sequentially read out via a signal line 56.

  The radiation image information read from each pixel 50 connected to the selected gate line 54 of the radiation detector 30 is amplified by each amplifier 62, then sampled by each sample hold circuit 64, and passed through the multiplexer 66. Is supplied to the A / D converter 70 and converted into a digital signal. The radiation image information converted into the digital signal is temporarily stored in the image memory 84 of the control unit 34.

  Similarly, the address decoder 60 of the line scan driver 58 sequentially switches the switch SW1 according to the address signal supplied from the address signal generator 82, and the charge held in each pixel 50 connected to each gate line 54. Radiation image information as information is read out through the signal line 56 and stored in the image memory 84 of the control unit 34 through the multiplexer 66 and the A / D converter 70.

  The radiation image information stored in the image memory 84 is transmitted to the console 22 by wireless communication via the transceiver 36. The console 22 performs predetermined image processing on the received radiation image information, and then stores the radiation image information in association with the registered patient information of the patient 14. The radiographic image information subjected to the image processing is transmitted from the console 22 to the display device 20, and the display device 20 displays the radiographic image information.

  When the doctor or radiologist turns off the power switch after the imaging of the patient 14 is completed, the power supply from the battery 32 to the radiation detector 30, the control unit 34, and the transmitter / receiver 36 is stopped, and the drive circuit IC 80a and the readout circuit The IC 80b, the control unit 34, and the transmitter / receiver 36 stop operating. Thereafter, a doctor or a radiographer can take up the radiation detection device 18 in a roll shape and store the radiation detection device 18 in a storage box.

  As described above, according to the radiation detection apparatus 18 and the radiation imaging system 10 according to the present embodiment, the sealing protective film 44 is formed so as to cover the grid 38, the sensor substrate 40, and the lead sheet 42. Therefore, the waterproofness, moistureproofness, and impact resistance of the radiation detector 30 having flexibility can be improved, and the reliability of the radiation detector 18 can be improved. Therefore, for example, when the radiation detection device 18 is used in an operating room or the like, blood and other germs may adhere, but the radiation detection device 18 is waterproof, hermetically sealed, moisture-proof, and impact resistant. Since it has a structure, it can be sterilized and washed as necessary, and one radiation detection device 18 can be used repeatedly. This also leads to lower running costs.

  In this embodiment, when the sealing protective film 44 is formed by a hot laminating method, the sealing protective film 44 that can be formed at a heating temperature of 180 ° C. or lower, preferably 150 ° C. or lower is used. Therefore, it is possible to avoid the influence of heat on the various circuits constituting the radiation detector 30, the scintillator 72, and the like during lamination. Further, since the sealing protective film 44 has a light shielding property, the influence of external light on the radiation detector 30 can be reduced.

  Further, for example, as a surface base material of the sealing protective film 44, by using a film coated with a metal foil such as aluminum or copper, a film deposited with a metal such as aluminum, a film in which metal fine powder is dispersed, etc. By making the sealing protective film 44 conductive, the influence of external radio waves and static electricity on the radiation detector 30 can be reduced, and high S / N of radiation image information can be achieved. In this case, it is preferable that the antenna of the transceiver 36 protrudes from the sealing protective film 44.

  In this embodiment, the scintillator 72, the TFT layer 74, and the photoelectric conversion layer 76 are stacked in this order on the flexible substrate 71 (the photoelectric conversion layer 76 and the TFT layer from the irradiation surface 30a toward the flexible substrate 71). 74 and the scintillator 72 are arranged in this order), so that visible light generated in the scintillator 72 can be efficiently converted into an electrical signal by the photoelectric conversion layer 76. As a result, high-quality radiation image information is obtained. be able to.

  Furthermore, since the radiation detector 18 incorporating the radiation detector 30 can be wound into a roll and stored in a storage box or the like when the radiation 12 is not irradiated, the handling of the radiation detector 18 is remarkably improved. can do.

  Furthermore, in the present embodiment, since signals are transmitted and received by radio communication between the console 22, the radiation detection device 18, the radiation source 16, and the display device 20, a cable for transmitting and receiving signals becomes unnecessary. There is no risk of disturbing the work of doctors or radiographers. Therefore, the doctor or radiologist can perform his / her work efficiently.

  Furthermore, in the present embodiment, the radiographic image information is captured based on the operation of the imaging switch of the radiation source 16 by the doctor or radiographer, but the radiographic image information is based on the operation of the console 22 by the doctor or radiographer. May be performed.

  In the above example, the sealing protective film 44 is formed so as to cover the grid 38, the sensor substrate 40, and the lead sheet 42. However, as shown in FIG. The lead sheet 42, the sensor substrate 40, and the grid 38 may be accommodated in the body 88, and the sealing protective film 44 may be formed so as to cover the grid 38 and the sensor substrate 40. In this case, a thermocompression bonding method under reduced pressure can be used. For example, the laminated body of the grid 38, the sensor substrate 40, and the lead sheet 42 accommodated in the casing 88 is accommodated in a vertically divided type chamber. After the chamber is sealed, the laminated body is defoamed by vacuuming. Then, the laminated protective film 44 is formed so as to cover the grid 38 and the sensor substrate 40 by pressing the laminated film onto the upper part of the laminated body with a diaphragm and further heating the laminated body and the laminated film. Can do.

  Moreover, in this Embodiment, you may replace the laminated structure of the radiation detector 30 with the structure of FIG. In FIG. 8, the TFT layer 74, the photoelectric conversion layer 76, and the scintillator 72 are laminated in this order from the flexible substrate 71 toward the irradiation surface 30a. Even in this case, since the visible light converted by the scintillator 72 can be converted into an electric signal by the photoelectric conversion layer 76, it is a matter of course that the above-described effects can be obtained.

  Furthermore, in this 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). May be converted to In this case, a film having no light shielding property can be used as the sealing protective film 44.

  Further, radiation image information can be acquired by using a light readout type radiation detector. In this optical readout type radiation detector, when radiation is incident on the solid detection elements arranged in a matrix, an electrostatic latent image corresponding to the dose is accumulated and recorded on the solid detection elements. When reading the electrostatic latent image, the radiation detector is irradiated with reading light from a flexible organic EL (Electro-Luminescence) panel or the like, and the value of the generated current is acquired as radiation image information. The radiation detector can erase and reuse the radiation image information that is the remaining electrostatic latent image by irradiating the radiation detector with erasing light (refer to Japanese Patent Laid-Open No. 2000-105297). .

  Furthermore, in the present embodiment, a storage phosphor panel that accumulates radiation energy as radiation image information in the phosphor and can extract the radiation image information as stimulated emission light by irradiating excitation light, You may comprise as the radiation detector 30 which has flexibility.

  In the radiation detector 30 described above, an example using the TFT 52 has been described. Alternatively, the radiation detector 30 may be implemented in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced by a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting the charges by a shift pulse corresponding to the gate signal referred to in the TFT 52.

  Further, the wireless communication between the radiation detection apparatus 18 and the external device may be performed by optical wireless communication using infrared rays or the like instead of normal communication using radio waves.

  Furthermore, it is more preferable to configure the radiation detection device 18 as shown in FIG.

  In other words, the guide line 504 serving as a reference for the imaging region and the imaging position is formed on the radiation detection device 18 on the irradiation surface 30a side. By using the guide line 504, the subject 14 (patient) is positioned with respect to the radiation detection device 18, and the irradiation range of the radiation 12 is set, so that radiographic image information can be recorded in an appropriate imaging region. .

  A display unit 506 that displays various types of information related to the radiation detection apparatus 18 is disposed in a region outside the imaging region of the radiation detection apparatus 18. The display unit 506 displays the ID information of the patient 14 recorded in the radiation detection device 18, the number of times the radiation detection device 18 is used, the cumulative exposure dose, and the state of charge of the battery 32 built in the radiation detection device 18 (remaining). Capacity), radiographic image information imaging conditions, positioning image of the patient 14 with respect to the radiation detection device 18 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 506, confirms in advance that the radiation detection apparatus 18 is in a usable state, and displays the displayed positioning image. Based on the above, it is possible to position the desired imaging region of the patient 14 in the radiation detection device 18 and to perform imaging of optimal radiation image information.

  Further, by forming a hole 508 in the radiation detection device 18 and tying the hole 508 with a string (not shown), the radiation detection device 18 can be easily handled and carried.

  Furthermore, it is preferable to arrange an input terminal 510 of the AC adapter, a USB (Universal Serial Bus) terminal 512, and a card slot 516 for loading the memory card 514.

  The input terminal 510 is connected to an external AC adapter when the charging function of the battery 32 built in the radiation detection apparatus 18 is deteriorated or when sufficient time for charging the battery 32 cannot be secured. The radiation detection device 18 can be immediately put into a usable state by supplying electric power from.

  The USB terminal 512 or the card slot 516 can be used when the radiation detection apparatus 18 cannot transmit and receive information by wireless communication with an external device such as the console 22. That is, by connecting a cable to the USB terminal 512, information can be transmitted / received to / from an external device by wired communication. In addition, information can be transmitted and received by loading a memory card 514 into the card slot 516, recording necessary information on the memory card 514, and then removing the memory card 514 and loading it into an external device.

  As shown in FIG. 10, a cradle 518 for charging the battery 32 built in the radiation detection device 18 is preferably disposed at a necessary location in the operating room or hospital. In this case, the cradle 518 not only charges the battery 32 but also transmits / receives necessary information to / from external devices such as the RIS 24, the HIS 26, and the console 22 using the wireless communication function or the wired communication function of the cradle 518. You may make it perform. The information to be transmitted and received can include radiation image information recorded in the radiation detection device 18 charged in the cradle 518.

  In addition, a display unit 520 is provided in the cradle 518 so that necessary information including the charging state of the radiation detection device 18 and the radiation image information acquired from the radiation detection device 18 is displayed on the display unit 520. It may be.

  In addition, a plurality of cradle 518 is connected to the network, and the charging state of the radiation detecting device 18 charged in each cradle 518 is collected via the network, and the location of the radiation detecting device 18 in a usable charging state is confirmed. It can also be configured to be able to.

  Of course, the radiation detection apparatus and the radiation imaging system according to the present invention are not limited to the above-described embodiments, and various configurations can be adopted without departing from the gist of the present invention.

It is a block diagram which shows the structure of the radiography system which concerns on this Embodiment. It is a perspective view which shows the radiation detection apparatus which concerns on this Embodiment. It is a perspective view which shows the radiation detection apparatus which concerns on this Embodiment partially fractured | ruptured. FIG. 4 is a cross-sectional view taken along line IV-IV in FIG. 3. It is explanatory drawing which shows the state which image | photographed the to-be-photographed object using the radiation detection apparatus which concerns on this Embodiment. It is a block diagram which shows the circuit structure of a radiation detector. It is sectional drawing which shows the other structural example along the IV-IV line of FIG. It is sectional drawing which shows the further another structural example along the IV-IV line of FIG. It is a perspective view which shows the other structural example of a radiation detection apparatus. It is a block diagram of the cradle which charges a radiation detection apparatus.

Explanation of symbols

10 ... Radiation imaging system 12 ... Radiation 14 ... Subject (patient)
16 ... Radiation source 18 ... Radiation detector 30 ... Radiation detector 40 ... Sensor substrate 44 ... Sealing protective film 72 ... Scintillator 74 ... TFT layer 76 ... Photoelectric conversion layer

Claims (10)

A radiation detector that detects radiation transmitted through a subject, converts the radiation into radiation image information, and has flexibility;
A radiation detection apparatus comprising: a sealing protective film that covers at least a part or all of the radiation detector and is made of a material that transmits the radiation. The radiation detection apparatus according to claim 1,
The radiation detector reads the electrical signal from the sensor substrate that converts the radiation into an electrical signal, a drive unit that drives the sensor substrate, and the sensor substrate that is driven by the drive unit. A reading unit for acquiring the radiation image information,
The radiation detection apparatus, wherein the sealing protective film is formed so as to cover at least the sensor substrate. The radiation detection apparatus according to claim 2.
The sensor substrate includes a scintillator that converts the radiation into visible light, and a solid-state detection element that converts the visible light into the electrical signal.
The radiation protective apparatus, wherein the sealing protective film has a light shielding property. The radiation detection apparatus according to claim 3.
The radiation detection apparatus, wherein the solid detection element and the scintillator are arranged in order of the subject, or the scintillator and the solid detection element are arranged in order. The radiation detection apparatus according to claim 1,
The radiation protection apparatus according to claim 1, wherein the sealing protective film is formed on at least the radiation irradiation side of the radiation detector. The radiation detection apparatus according to claim 5.
The sealing protective film is provided with an index serving as a reference for an imaging region and an imaging position. The radiation detection apparatus according to claim 1,
The radiation protective apparatus, wherein the sealing protective film has conductivity. The radiation detection apparatus according to claim 1,
The radiation detection apparatus, wherein the sealing protective film is formed by a hot laminating method and at a heating temperature of 180 ° C. or less.   A radiation imaging apparatus comprising: the radiation detection apparatus according to claim 1; a radiation source that outputs the radiation; and a control device that controls the radiation source and the radiation detection apparatus. system. The radiation imaging system according to claim 9,
The radiation detection system transmits the radiation image information converted by the radiation detector to the control device by wireless communication.

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