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WO2013015044A1 - Équipement radiographique - Google Patents

Équipement radiographique Download PDF

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Publication number
WO2013015044A1
WO2013015044A1 PCT/JP2012/065714 JP2012065714W WO2013015044A1 WO 2013015044 A1 WO2013015044 A1 WO 2013015044A1 JP 2012065714 W JP2012065714 W JP 2012065714W WO 2013015044 A1 WO2013015044 A1 WO 2013015044A1
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WO
WIPO (PCT)
Prior art keywords
radiation
unit
radiation detector
light emitting
light
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/JP2012/065714
Other languages
English (en)
Japanese (ja)
Inventor
大田　恭義
西納　直行
岩切　直人
中津川　晴康
北野　浩一
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Fujifilm Corp
Original Assignee
Fujifilm Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Fujifilm Corp filed Critical Fujifilm Corp
Publication of WO2013015044A1 publication Critical patent/WO2013015044A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4266—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a plurality of detector units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4283—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by a detector unit being housed in a cassette
    • G—PHYSICS
    • G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
    • G03B—APPARATUS OR ARRANGEMENTS FOR TAKING PHOTOGRAPHS OR FOR PROJECTING OR VIEWING THEM; APPARATUS OR ARRANGEMENTS EMPLOYING ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ACCESSORIES THEREFOR
    • G03B42/00—Obtaining records using waves other than optical waves; Visualisation of such records by using optical means
    • G03B42/02—Obtaining records using waves other than optical waves; Visualisation of such records by using optical means using X-rays
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • A61B6/542—Control of apparatus or devices for radiation diagnosis involving control of exposure

Definitions

  • the present invention relates to a radiation imaging apparatus capable of moving image shooting and still image shooting.
  • the radiation imaging apparatus includes a radiation generator that emits radiation (for example, X-rays) toward a subject, and a radiation detector that is disposed opposite to the radiation generator and detects and images radiation that has passed through the subject. .
  • Some of these radiation imaging apparatuses are capable of both moving image shooting (also referred to as fluoroscopic imaging) and still image shooting (also simply referred to as shooting).
  • the dose of radiation emitted from the radiation generator differs between when shooting moving images and when shooting still images. Movie shooting is performed at a low dose, and is used for positioning a patient for still image shooting, searching for a lesion, and the like. Still image capturing is performed at a high dose, and is used to obtain a clear radiographic image of a lesion. Generally, the dose during still image shooting is about 100 times the dose during moving image shooting.
  • Patent Document 1 since the radiographic apparatus described in Patent Document 1 performs moving image shooting and still image shooting using a single radiation detector, the image quality and the still image shooting can be reduced between moving image shooting and still image shooting.
  • the field of view size cannot be changed. Therefore, in Patent Documents 2 and 3, a first radiation detector for taking a still image and a second radiation detector for taking a moving image with a smaller visual field than the first radiation detector are provided.
  • a radiation imaging apparatus has been proposed in which the second radiation detector is retracted from the radiation irradiation region from the radiation generator and then the still image capturing is performed with the first radiation detector. .
  • the radiation imaging apparatus of the present invention includes a first radiation detector, a second radiation detector, a setting unit, and a control unit.
  • the first radiation detector detects the radiation emitted from the radiation generator and generates a charge.
  • the second radiation detector generates a charge by detecting the radiation transmitted through the first radiation detector.
  • the setting unit sets a charge readout region in a detection region where the second radiation detector detects radiation.
  • the control unit causes the first radiation detector to execute one of the still image shooting and the moving image shooting and drives only the readout region of the second radiation detector to execute the other of the still image shooting and the moving image shooting. .
  • control unit preferably drives the first radiation detector to execute still image shooting, and drives the readout region of the second radiation detector to execute moving image shooting. In this case, it is preferable that the control unit drives the second radiation detector at a higher frame rate than the first radiation detector.
  • the first radiation detector and the second radiation detector are panels having the same area size.
  • a radiation dose measuring unit that measures the dose of the radiation pulse emitted from the radiation generator
  • a dose determination unit that compares the dose measured by the radiation dose measuring unit with a predetermined threshold.
  • the control unit drives the readout region of the second radiation detector to execute moving image shooting, and determines the dose.
  • the first radiation detector is driven to execute still image shooting.
  • the setting unit sets the readout area based on the position of the radiation generator.
  • the setting unit may set the readout region based on the radiation irradiation range detected by the first radiation detector.
  • the first radiation detector is disposed on the radiation incident side of the light emitting unit that absorbs radiation and generates visible light, and converts the visible light generated by the light emitting unit into charges.
  • the second radiation detector is arranged on the side opposite to the radiation incident side of the light emitting unit and converts the visible light generated by the light emitting unit into an electric charge. It is preferable that it is comprised by the 2nd photon detection part to do.
  • the light emitting portion includes a columnar crystal phosphor, and the tip portion of the columnar crystal phosphor faces the first light detection unit.
  • the first radiation detector is disposed on the radiation incident side of the first light emitting unit that absorbs radiation and generates visible light, and is generated by the first light emitting unit. And a second radiation detector that absorbs the radiation transmitted through the first light emitting unit and the first light detection unit and converts the visible light into visible light.
  • one of the first light emitting unit and the second light emitting unit includes a columnar crystal phosphor and the other includes a GOS phosphor.
  • the second radiation detector since the second radiation detector detects the radiation transmitted through the first radiation detector, the first and second radiation detectors perform moving image capturing. While shooting, still images can be taken quickly. Further, since the second radiation detector is driven only in the readout region set in the radiation detection region, the calorific value is small and the temperature rise is suppressed.
  • a radiation information system (RIS) 10 is a system for managing information such as medical appointments and diagnosis records in a radiology department in a hospital.
  • the RIS 10 is configured by connecting a plurality of terminal apparatuses 11, an RIS server 12, and a radiation imaging system 13 installed in each radiation imaging room (or operating room) in a hospital to a hospital network NW by wire or wirelessly.
  • a radiation imaging system 13 installed in each radiation imaging room (or operating room) in a hospital to a hospital network NW by wire or wirelessly.
  • a personal computer (PC) or the like is used, which is operated by a photographer (doctor or radiographer). The photographer operates the terminal device 11 to input / view diagnostic information and facility reservation. A radiographic imaging request (imaging reservation) is also input via the terminal device 11.
  • the RIS server 12 is a computer including a storage unit 12A that stores an RIS database (DB).
  • the storage unit 12A stores patient attribute information (patient name, sex, date of birth, age, blood type, patient ID, etc.), medical history, medical history, history of radiographic imaging, and radiographic images taken in the past. Other information related to the patient such as data and information related to the electronic cassette 15 included in each radiation imaging system 13 (identification number, model, size, sensitivity, usable imaging part, date of use start, number of times of use, etc.) are registered. ing.
  • the RIS server 12 is a process for managing the entire RIS 10 based on the information registered in the storage unit 12A (for example, a process for receiving an imaging request from each terminal device 11 and managing an imaging schedule of each radiation imaging system 13). )I do.
  • the radiation imaging system 13 captures a radiation image instructed from the RIS server 12 according to the operation of a doctor or a radiographer.
  • the radiation imaging system 13 includes a radiation generator 14 that generates radiation, an electronic cassette 15 that detects radiation transmitted through an imaging region of a patient and generates a radiation image, a cradle 16 that charges the electronic cassette 15, and these And a console 17 for controlling the operation of each device.
  • the electronic cassette 15 is a portable radiation imaging apparatus.
  • the radiation imaging room includes a radiation generator 14, a standing table 20 used for radiography (hereinafter referred to as standing imaging) of an imaging region of a standing patient 20 ⁇ / b> A, and a patient in a prone position.
  • a supine table 21 used for radiographing (hereinafter referred to as supine imaging) the 21A imaging region is provided.
  • the standing base 20 is provided with a cassette chamber 22 in which the electronic cassette 15 is mounted.
  • the electronic cassette 15 is held in the cassette chamber 22 of the standing base 20.
  • the electronic cassette 15 is stored in the cassette chamber 23 of the supine table 21.
  • the radiation generator 14 is supported on the ceiling 26 while supporting the telescopic support 25.
  • a moving mechanism 24 that moves two-dimensionally is provided.
  • pillar 25 is supporting the radiation generator 14 so that rotation of the surroundings of a horizontal axis (arrow A direction) and a vertical axis (arrow B direction) is possible.
  • the cradle 16 is formed with an accommodating portion 16A capable of accommodating the electronic cassette 15.
  • the electronic cassette 15 is accommodated in the accommodating portion 16A when not in use, and the built-in battery is charged in this state.
  • the electronic cassette 15 is taken out from the cradle 16 by the photographer at the time of radiographic image capture, and is held by the holding unit 22 of the stand 20 in the case of standing position imaging, and the supine table 21 in the case of position capturing. Is accommodated in the cassette chamber 23.
  • the electronic cassette 15 includes a housing 30, a radiation dose measurement sensor 31, a first light detection unit 32, a light emission unit 33, a second light detection unit 34, a base 35, and a storage case 36.
  • the radiation dose measuring sensor 31, the first light detection unit 32, the light emitting unit 33, the second light detection unit 34, and the base 35 are in the form of a panel having the same area. They are stacked in order in the housing 30.
  • having the same area includes not only having the same area but also substantially the same.
  • the housing 30 is made of a radiation transmissive material and has an overall shape of a rectangular parallelepiped.
  • the housing 30 has a top plate 30A formed of a low radiation absorbing material such as carbon.
  • the top plate 30A is irradiated with radiation that has passed through the imaging region of the patient. Portions other than the top plate 30A of the housing 30 are made of ABS resin or the like.
  • the top plate 30A is composed of a plurality of light emitting diodes (LEDs), and displays an operation state such as an operation mode (for example, “ready state” or “data transmitting”) of the electronic cassette 15 and a remaining battery capacity.
  • a display unit 37 is provided. Note that the display unit 37 may be a display device configured by light emitting elements other than LEDs, a liquid crystal display, or an organic EL display. Moreover, you may provide the display part 37 in parts other than the top plate 30A.
  • the storage case 36 is provided along one end side in the longitudinal direction of the top plate 30A.
  • the storage case 36 stores a microcomputer (not shown) and a battery (not shown).
  • the battery is chargeable and detachable.
  • Various electronic circuits of the electronic cassette 15 including the radiation dose measuring sensor 31, the first light detection unit 32, and the second light detection unit 34 are operated by electric power supplied from the battery.
  • a radiation shielding member such as a lead plate is provided on the top plate 30 ⁇ / b> A side of the storage case 36.
  • the first light detection unit 32 is configured by forming a plurality of pixels 324 including a photoelectric conversion unit 321, a thin film transistor (TFT: Thin Film Transistor) 322, and a capacitor 323 over an insulating substrate 325. ing.
  • the pixels 324 are arranged in a two-dimensional matrix.
  • the insulating substrate 325 and the layer on which the TFT 322 and the capacitor 323 are formed constitute a so-called TFT active matrix substrate (hereinafter referred to as a TFT substrate) 32A.
  • the TFT 322 is made of amorphous silicon.
  • the insulating substrate 325 is formed of a material having light transmissivity, such as a quartz substrate, a glass substrate, and a resin substrate, and having little radiation absorption.
  • the photoelectric conversion unit 321 includes a first electrode 321A and a second electrode 321B, and a photoelectric conversion film 321C disposed therebetween.
  • the photoelectric conversion film 321C is formed of amorphous silicon, and absorbs visible light emitted from the light emitting unit 33 described later to generate charges.
  • the photoelectric conversion unit 321 constitutes a PIN-type or MIS-type photodiode and is provided on the TFT substrate 32A.
  • a planarizing layer 326 that covers the photoelectric conversion unit 321 is provided on the TFT substrate 32A.
  • the planarization layer 326 is formed of silicon nitride, silicon oxide, or the like, and the surface opposite to the radiation incident side is planarized.
  • the second light detection unit 34 has the same configuration as that of the first light detection unit 32, and the pixels 344 including the photoelectric conversion unit 341, the TFT 342, and the capacitor 343 are arranged in a two-dimensional matrix on the insulating substrate 345. A plurality are formed.
  • the photoelectric conversion unit 341 includes a first electrode 341A and a second electrode 341B, and a photoelectric conversion film 341C disposed therebetween.
  • a planarization layer 346 that covers the photoelectric conversion portion 341 is provided, and the planarization layer 346 has a plane on the radiation incident side that is planarized.
  • the insulating substrate 345 and the layer on which the TFT 342 and the capacitor 343 are formed constitute the TFT substrate 34A.
  • the configuration order of each part with respect to the radiation incident direction is opposite to the configuration order of each part of the first light detection unit 32. That is, the planarization layer 326 of the first light detection unit 32 and the planarization layer 346 of the second light detection unit 34 face each other, and the light emitting unit 33 is disposed therebetween.
  • the light emitting unit 33 generates and emits visible light in response to the incidence of radiation.
  • the second light detection unit 34 has substantially the same planar shape and area as the first light detection unit 32.
  • the planarizing layer 326 of the first light detection unit 32 and the light emitting unit 33 are bonded to each other by a light-transmitting adhesive layer 327.
  • the planarization layer 346 of the second light detection unit 34 and the light emitting unit 33 are bonded to each other with a light-transmitting adhesive layer 347.
  • the insulating substrate 345 of the second light detection unit 34 is bonded to the base 35 with an adhesive layer 348.
  • a radiation dose measuring sensor 31 is formed on the radiation incident side of the first light detection unit 32.
  • a wiring layer 311, an insulating layer 312, a photoelectric conversion unit 313, and a protective layer 314 are sequentially formed on an insulating substrate 325.
  • the wiring layer 311 is a layer in which a wiring 73 (see FIG. 7) described later is patterned on the insulating substrate 315.
  • the photoelectric conversion unit 313 is an element that detects visible light emitted from the light emitting unit 33 and transmitted through the first light detection unit 32, and a plurality of photoelectric conversion units 313 are formed on the insulating layer 312 in a matrix.
  • the thickness of the radiation dose measuring sensor 31 is about 0.05 mm.
  • the photoelectric conversion unit 313 includes a first electrode 313A and a second electrode 313B, and a photoelectric conversion film 313C disposed therebetween.
  • the photoelectric conversion film 313C is formed of an organic photoelectric conversion material.
  • the photoelectric conversion film 313C is formed by applying an organic photoelectric conversion material onto the second electrode 313B using an inkjet head or the like.
  • the light emitting unit 33 includes a vapor deposition substrate 331, a scintillator 332, and a moisture-proof protective film 333.
  • the vapor deposition substrate 331 is a light transmissive substrate such as a quartz substrate, a glass substrate, or a resin substrate.
  • the scintillator 332 is formed by vapor depositing thallium activated cesium iodide (CsI: Tl) on the vapor deposition substrate 331.
  • the scintillator 332 includes a non-columnar crystal 332A and a plurality of columnar crystals 332B provided on the non-columnar crystal 332A.
  • the moisture-proof protective film 333 is formed of a light-proof moisture-proof material (for example, polyparaxylylene) and covers the periphery of the scintillator 332.
  • the vapor deposition substrate 331 is not necessarily provided.
  • the vapor deposition substrate 331 may be peeled off from the scintillator 332, and the scintillator 332 may be bonded to the second light detection unit 34.
  • the scintillator 332 may be directly deposited on the second light detection unit 34.
  • a phosphor material such as sodium activated cesium iodide (CsI: Na) may be used.
  • the tip portion 332 ⁇ / b> C of the columnar crystal 332 ⁇ / b> B is arranged to face the first light detection unit 32.
  • the vapor deposition substrate 331 is bonded to the second light detection unit 34 with an adhesive or the like.
  • the plurality of columnar crystals 332B are separated from each other through the gap GP.
  • the diameter of each columnar crystal 332B is about several ⁇ m to 10 ⁇ m.
  • the scintillator 332 absorbs radiation that is emitted from the radiation generator 14 and passes through the patient, the top plate 30A, the radiation dose measurement sensor 31, the first light detection unit 32, and the like and is incident on the light emitting unit 33 to generate visible light. appear. Since radiation enters the scintillator 332 from the first light detection unit 32 side, light emission in the scintillator 332 occurs mainly on the distal end portion 332C side. Visible light generated in the scintillator 332 travels toward the first light detection unit 32 and the second light detection unit 34 by the light guide effect of the columnar crystal 332B.
  • the visible light that has traveled toward the first light detection unit 32 is emitted from the pointed tip 332C, passes through the moisture-proof protective film 333, and enters the first light detection unit 32.
  • the first light detection unit It is detected by 32 photoelectric conversion units 321. Further, part of the visible light incident on the first light detection unit 32 passes through the first light detection unit 32 and enters the radiation dose measurement sensor 31. Visible light incident on the radiation dose measurement sensor 31 is detected by the photoelectric conversion unit 313.
  • the light emitting unit 33 and the first light detection unit 32 constitute a first radiation detector 40.
  • the first radiation detector 40 is arranged in the order of the first light detection unit 32 and the light emitting unit 33 along the radiation traveling direction.
  • Such an arrangement method is called an ISS (Irradiation Side Sampling) type.
  • the light emitting unit 33 and the second light detection unit 34 constitute a second radiation detector 41.
  • the second radiation detector 41 is arranged in the order of the light emitting unit 33 and the second light detection unit 34 along the radiation traveling direction.
  • PSS Penetration Side Sampling
  • the light emitting unit 33 and the radiation dose measuring sensor 31 constitute an ISS type radiation dose measuring unit 42.
  • the first radiation detector 40 detects a high-definition image with a large amount of incident light.
  • the second radiation detector 41 is away from the light emitting position, the amount of incident light is small.
  • the first radiation detector 40 having a large incident light amount is used for still image shooting.
  • the second radiation detector 41 having a small incident light amount is used for moving image shooting.
  • the first photodetecting portion 32 extends along the row direction, and includes a plurality of gate wirings 50 for turning on / off each TFT 322, and a column direction intersecting the row direction.
  • a plurality of data wirings 51 are provided for reading out the charges accumulated in the capacitor 323 through the TFT 322 in the on state.
  • the first radiation detector 40 is provided with a gate line driver 52, a signal processing unit 53, and an image memory 54 in addition to the first light detection unit 32.
  • the gate wiring 50 is connected to the gate line driver 52.
  • the data wiring 51 is connected to the signal processing unit 53.
  • the TFTs 322 When charges are accumulated in the capacitor 323, the TFTs 322 are sequentially turned on in units of rows by a signal supplied from the gate line driver 52 via the gate wiring 50.
  • the electric charge accumulated in the capacitor 323 of the pixel 324 in which the TFT 322 is turned on is transmitted through the data wiring 51 as an analog electric signal and input to the signal processing unit 53. In this way, the charges accumulated in the capacitor 323 of each pixel 324 are sequentially read out in units of rows.
  • the signal processing unit 53 includes an amplifier (not shown) and a sample hold circuit (not shown) for each data wiring 51.
  • the electric signal transmitted through each data line 51 is amplified by an amplifier and then held in a sample and hold circuit.
  • a multiplexer (not shown) and an A / D converter (not shown) are sequentially connected to the output side of the sample hold circuit.
  • the electric signal held in each sample and hold circuit is selected by a multiplexer and converted into digital image data by an A / D converter.
  • An image memory 54 is connected to the signal processing unit 53, and image data output from the A / D converter of the signal processing unit 53 is stored in the image memory 54.
  • the second light detection unit 34 is provided with a plurality of gate wirings 60 and a plurality of data wirings 61.
  • the second radiation detector 41 is provided with a gate line driver 62, a signal processing unit 63, and an image memory 64 in addition to the second light detection unit 34.
  • the gate line 60 is connected to the gate line driver 62, and the data line 61 is connected to the signal processing unit 63.
  • An image memory 64 is connected to the signal processing unit 63.
  • the image memories 54 and 64 are connected to a cassette control unit 70 that controls the overall operation of the electronic cassette 15.
  • the cassette control unit 70 is a microcomputer, and includes a CPU 70A, a RAM 70B, and a nonvolatile ROM 70C such as a flash memory.
  • the cassette control unit 70 is connected to a wireless communication unit 71 that wirelessly transmits and receives various types of information to and from external devices.
  • the wireless communication unit 71 corresponds to a wireless LAN (Local Area Network) standard represented by IEEE (Institute of Electrical and Electronics Electronics) (802.11a / b / g / n).
  • the cassette control unit 70 performs wireless communication with the console 17 via the wireless communication unit 71.
  • the radiation dose measuring unit 42 is used for measuring the dose of radiation (radiation dose per unit time) irradiated to the electronic cassette 15 from the radiation generator 14.
  • the radiation generator 14 emits, as radiation, a low-dose pulse for moving image shooting and a high-dose pulse for still image shooting according to the operation of the photographer.
  • the radiation dose measurement sensor 31 of the radiation dose measurement unit 42 is provided with the same number of wirings 73 as the photoelectric conversion unit 313.
  • the radiation dose measurement unit 42 is provided with a signal detection unit 74.
  • Each photoelectric conversion unit 313 is connected to the signal detection unit 74 via a dedicated wiring 73.
  • the signal detection unit 74 includes an amplifier, a sample hold circuit, and an A / D converter (all not shown) for each wiring 73, and is connected to the cassette control unit 70 and the dose determination unit 75.
  • the signal detection unit 74 performs sampling of a signal transmitted from the photoelectric conversion unit 313 via the wiring 73 in a predetermined cycle under the control of the cassette control unit 70, converts the sampled signal into digital data, and determines the dose.
  • the data are sequentially output to the unit 75.
  • the dose determination unit 75 determines the dose of radiation emitted from the radiation generator 14 based on the data input from the signal detection unit 74 (that is, a low-dose pulse for moving image shooting and a high-dose pulse for still image shooting). To determine which of the two). This determination result is output to the cassette control unit 70.
  • the electronic cassette 15 is provided with a power supply unit 77 and is connected to the various electronic circuits described above by wiring (not shown).
  • the power supply unit 77 incorporates the above-described battery so as not to impair the portability of the electronic cassette 15, and supplies power from the battery to various electronic circuits.
  • the power supply unit 77 is connected to the cassette control unit 70.
  • the cassette controller 70 can selectively turn on / off the power supply to the first radiation detector 40 and the second radiation detector 41.
  • the gate line driver 62 of the second radiation detector 41 is composed of a plurality of drive circuits 62A.
  • the signal processing unit 63 includes a plurality of processing circuits 63A.
  • the drive circuit 62A and the processing circuit 63A are set to an active state (Enable) or an inactive state (Disable) by a control signal from the cassette control unit 70, respectively.
  • the cassette control unit 70 selects the drive circuit 62A and the processing circuit 63A that are set to “Enable” in accordance with the position of the radiation generator 14 in the XY directions, so that the second photodetection unit 34 is in the detection area DA. Then, a readout area RA for reading out the charges is set.
  • the plurality of drive circuits 62A and the processing circuit 63A constitute a setting unit for the read area RA.
  • the drive circuit 62A and the processing circuit 63A set to “Disable” consume less power and generate less heat than the drive circuit 62A and the processing circuit 63A set to “Enable”.
  • the gain of the amplifier included in the processing circuit 63A is set to a value larger than the gain of the amplifier included in the signal processing unit 53 in the first radiation detector 40. Has been. Except for the gain of the amplifier, the configuration of the second radiation detector 41 is the same as that of the first radiation detector 40, and a detailed description thereof will be omitted.
  • a console 17 is composed of a computer, a CPU 170 that controls the operation of the entire apparatus, a ROM 171 that stores various programs including a control program in advance, a RAM 172 that temporarily stores various data, And an HDD 173 for storing data, which are connected to each other via a bus line BL.
  • a communication I / F 174 and a wireless communication unit 175 are connected to the bus line BL, and a display 176 is connected via a display driver 177.
  • an operation unit 178 is connected to the bus line BL via an operation input detection unit 179.
  • the communication I / F 174 is connected to the connection terminal 14A of the radiation generator 14 via the connection terminal 17A and the communication cable 78.
  • the CPU 170 transmits and receives information such as the exposure conditions to and from the radiation generator 14 by a wired method using the communication I / F 174 and the like.
  • the wireless communication unit 175 communicates with the wireless communication unit 71 of the electronic cassette 15 and transmits and receives various types of information such as image data between the CPU 170 and the electronic cassette 15.
  • the display driver 177 generates and outputs a signal for displaying various information on the display 176.
  • the CPU 170 displays an operation menu, a radiation image, and the like on the display 176 via the display driver 177.
  • the operation unit 178 includes a keyboard and the like, and various information and operation instructions are input thereto.
  • the operation input detection unit 179 detects an operation on the operation unit 178 and transmits a detection result to the CPU 170.
  • the operation unit 178 is connected to a foot switch (not shown) that is arranged on the floor of the radiation imaging room and performs switching between moving image shooting and still image shooting. The foot switch is turned on / off when the photographer steps on the foot.
  • the radiation generator 14 performs radiation based on the radiation I / F 141 that transmits and receives various information such as the exposure conditions between the radiation source 140 that generates radiation and the console 17, and the exposure conditions received from the console 17.
  • a radiation source control unit 142 that controls the source 140 and a position detection device 143 that detects the position of the radiation generator 14 in the XY directions are provided.
  • the position detection device 143 is composed of a potentiometer or the like.
  • the position information of the radiation generator 14 detected by the position detection device 143 is transmitted to the console 17 via the communication I / F 141, and is transmitted from the wireless communication unit 175 of the console 17 to the electronic cassette 15.
  • the position information of the radiation generator 14 is received by the wireless communication unit 71.
  • the cassette control unit 70 selects the drive circuit 62A and the processing circuit 63A to be set to “Enable” based on the position information of the radiation generator 14. Thereby, the readout area RA is set according to the position of the radiation generator 14.
  • an imaging request is input from the terminal device 11.
  • a patient to be imaged an imaging region to be imaged are designated, and tube voltage, tube current, etc. are designated as necessary.
  • the RIS server 12 notifies the RIS server 12 of the content of the input photographing request.
  • the RIS server 12 stores the content of the imaging request notified from the terminal device 11 in the storage unit 12A.
  • the console 17 accesses the RIS server 12 to acquire the content of the imaging request and the attribute information of the patient to be imaged, and displays the content of the imaging request and the attribute information of the patient on the display 176 (see FIG. 9). .
  • the radiographer performs preparatory work for radiographic imaging based on the content of the radiography request displayed on the display 176. For example, when photographing the affected part of the patient 21 ⁇ / b> A lying on the prone table 21, the electronic cassette 15 is stored in the cassette chamber 23 of the prone table 21.
  • the photographer When the preparatory work is completed, the photographer performs an operation for notifying the completion of the preparatory work through the operation unit 178 of the console 17. Using this operation as a trigger, the console 17 sets the operation mode of the electronic cassette 15 to the ready state.
  • the radiation control unit 70 drives the radiation dose measurement unit 42 and the dose determination unit 75 to irradiate the radiation pulse (a low-dose pulse for moving image shooting or a still image).
  • a standby operation for detecting a high-dose pulse for imaging) is started.
  • the console 17 notifies the photographer that the camera is ready to shoot by switching the display on the display 176.
  • the photographer who has confirmed this notification issues a shooting instruction via the operation unit 178.
  • the console 17 transmits an instruction signal instructing the start of exposure to the radiation generator 14.
  • the radiation generator 14 emits a high-dose pulse for taking a still image from the radiation generator 14 with a tube voltage and a tube current corresponding to the exposure conditions received from the console 17.
  • the image data obtained by 40 is transmitted to the console 17 via the wireless communication unit 71.
  • the input image data is displayed on the display 176 as a still image.
  • the radiation generator 14 irradiates the patient with a low-dose pulse for moving image shooting at a predetermined interval.
  • the cassette control unit 70 selects the drive circuit 62A and the processing circuit 63A to be set to “Enable” based on the position information of the radiation generator 14 sequentially detected by the position detection device 143, and the second light A read area RA having a predetermined size is set in the detection area DA of the detector 34.
  • the cassette control unit 70 controls the collimator 140A to match the shape and size of the radiation irradiation area with the reading area RA.
  • the radiation dose measurement unit 42 performs sampling of radiation at intervals shorter than the irradiation interval of the low-dose pulse.
  • the dose determination unit 75 compares the radiation dose at the time of rising of the radiation measured by the radiation dose measurement unit 42 with a predetermined threshold, and when the radiation dose (intensity) is smaller than this threshold, it is determined as a low dose pulse. To do.
  • the cassette control unit 70 drives the second radiation detector 41 in synchronization with the low-dose pulse to execute the moving image capturing operation MP.
  • this moving image shooting operation MP all the gate wirings 60 are selected at once by the gate line driver 62, all the TFTs 342 are turned on, and the electric charge accumulated in the capacitor 343 is discarded (reset).
  • the capacitor 343 enters a charge accumulation state.
  • the photoelectric conversion unit 341 generates charges corresponding to the radiation that has passed through the imaging region of the patient and accumulates them in the capacitor 343.
  • the gate wiring 60 in the readout region RA is sequentially driven by the gate line driver 62, and the charge accumulated in the capacitor 343 of the pixel portion 344 included in the readout region RA is turned on.
  • the TFT 342 in the state is output to the signal processing unit 63 via the data wiring 61, and image data is generated by the signal processing unit 63.
  • the cassette control unit 70 stops the supply of the power supply voltage from the power supply unit 77 to each part of the first radiation detector 40 and turns it off. Thereby, the influence of the power supply noise on the reading operation of the second radiation detector 41 is reduced.
  • a moving image capturing operation MP is performed, and image data is sequentially transmitted from the image memory 64 to the console 17 via the wireless communication unit 71.
  • the input image data is displayed on the display 176 as a moving image.
  • a high-dose pulse for still image photographing is emitted from the radiation generator 14 toward the imaging region of the patient.
  • the dose of this high dose pulse is about 100 times that of the low dose pulse.
  • the dose determination unit 75 compares the radiation dose at the time of rising of the radiation detected by the radiation dose measurement unit 42 with a predetermined threshold value, and determines that the dose is a high dose pulse when the radiation dose is larger than this threshold value.
  • the cassette control unit 70 drives the first radiation detector 40 in synchronization with the high-dose pulse to execute the still image capturing operation SP.
  • This still image capturing operation SP is performed by activating all gate wirings 50 and data wirings 51 of the first light detection unit 32 (set to “Enable”), and the signal processing unit 63 performs high-definition image processing. Data is generated.
  • This image data is transmitted to the console 17 via the wireless communication unit 71, and is displayed on the display 176 as a still image on the console 17. Note that this still image may be displayed on another display other than the display 176.
  • moving images and still images are stored in a memory for postoperative examination.
  • the cassette control unit 70 stops the supply of the power supply voltage from the power supply unit 77 to each part of the second radiation detector 41 and turns it off (OFF). Thereby, the influence of the power supply noise on the reading operation of the first radiation detector 40 is reduced.
  • the second radiation detector 41 is driven only in the reading area RA set in the detection area DA of the second light detection unit 34.
  • the number of pixel units 344 included in the readout area RA (the number of effective pixels at the time of moving image shooting) is the number of pixel units 322 included in the detection region of the first light detection unit 32 (the number of effective pixels at the time of still image shooting). Therefore, at the time of moving image shooting, it is driven at a high speed and a moving image is generated at a high frame rate.
  • first radiation detector 40 and the second radiation detector 41 are stacked in the radiation traveling direction, and the second radiation detector 41 detects the radiation transmitted through the first radiation detector 40. Therefore, when switching from moving image shooting to still image shooting, it is not necessary to move the second radiation detector 41, and quick still image shooting is performed.
  • the second radiation detector 41 uses the second light detection unit 34 configured using the TFT substrate 34A, but a silicon substrate is used as the second light detection unit 34. It is also possible to use a CMOS image sensor or a CCD image sensor configured as a base. Thereby, the second radiation detector 41 can be driven at a higher speed. Furthermore, it is also preferable to use a wide gap semiconductor substrate such as silicon carbide (SiC) instead of the silicon substrate.
  • SiC substrate is advantageous in that it has about 500 times higher radiation resistance than the silicon substrate.
  • the radiation dose measurement sensor 31, the first light detection unit 32, the first light emission unit 33A, the second light detection unit 34, and the second light emission unit are arranged along the radiation traveling direction. 33B are arranged in order.
  • the first light emitting unit 33A and the second light emitting unit 33B have the same configuration as the light emitting unit 33 described above.
  • the first radiation detector 40 is an ISS type radiation detector composed of a first light detection unit 32 and a first light emitting unit 33A
  • the second radiation detector 41 is a first radiation detector 41.
  • This is an ISS type radiation detector composed of two light detectors 34 and a second light emitter 33B.
  • the light reflecting layer 81A is formed on the surface opposite to the radiation incident side of the first light emitting portion 33A, and the light reflecting layer 81B is formed on the surface opposite to the radiation incident side of the second light emitting portion 33B. It is preferable to form.
  • the light reflecting layers 81A and 81B are formed of a metal film such as aluminum.
  • the radiation dose measurement sensor 31, the first light emitting unit 33 ⁇ / b> A, the first light detecting unit 32, the second light emitting unit 33 ⁇ / b> B, and the second light detecting unit are arranged along the radiation traveling direction. 34 are arranged in order.
  • the first radiation detector 40 is a PSS type radiation detector composed of a first light detection unit 32 and a first light emitting unit 33A
  • the second radiation detector 41 is a first radiation detector 41.
  • 2 is a PSS type radiation detector composed of two light detectors 34 and a second light emitter 33B.
  • the first radiation detector 40 and the second radiation detector 41 are both PSS type.
  • the light reflecting layer 81A is formed on the radiation incident side surface of the first light emitting unit 33A
  • the light reflecting layer 81B is formed on the radiation incident side surface of the second light emitting unit 33B.
  • the radiation dose measurement sensor 31, the second light detection unit 34, the first light detection unit 32, and the light emitting unit 33 are sequentially arranged along the radiation traveling direction.
  • each of the first radiation detector 40 and the second radiation detector 41 is an ISS type.
  • the second light detection unit 34 is preferably formed of an organic material, like the radiation dose measurement sensor 31.
  • the radiation dose measurement sensor 31, the first light detection unit 32, the first light emission unit 33 ⁇ / b> A, the second light emission unit 33 ⁇ / b> B, and the second light detection unit are arranged along the radiation traveling direction. 34 are arranged in order.
  • the light emitting unit 33 is composed of a first light emitting unit 33A and a second light emitting unit 33B.
  • the first radiation detector 40 is an ISS type radiation detector composed of a first light emitting unit 33A and a first light detecting unit 32
  • the second radiation detector 41 is a second light emitting unit. This is a PSS type radiation detector composed of 33B and the second light detection unit.
  • the first light emitting unit 33A and the second light emitting unit 33B include phosphors having different characteristics.
  • a columnar crystal phosphor having a columnar crystal structure such as CsI: Tl or CsI: Na is used for the first light emitting unit 33A
  • a gadolinium oxide (GOS) phosphor is used for the second light emitting unit 33B.
  • GOS gadolinium oxide
  • the columnar crystal phosphor has high resolution and high performance, it is more expensive than the GOS phosphor. Therefore, the columnar crystal phosphor is the first of the first radiation detector 40 for still image shooting that requires high-quality shooting.
  • a columnar crystal phosphor is used for the light emitting unit 33A, and a GOS phosphor is used for the second light emitting unit 33B of the second radiation detector 41 for moving image shooting that does not require high image quality. This can reduce costs without sacrificing the desired performance.
  • the columnar crystal phosphor has a shock resistance that deteriorates as the thickness increases. However, in this configuration, the columnar crystal phosphor can be thinned, and thus the impact resistance is improved.
  • GOS phosphors are powder particles, they are mixed in a binder resin. Since the resolution can be improved by making the GOS phosphor small particles, the GOS phosphor is used for the first light emitting portion 33A and the columnar crystal fluorescence is used for the second light emitting portion 33B.
  • the body may be used. In this case, it is preferable that the tip of the columnar crystal phosphor is opposed to the first light detection unit 34.
  • the first light emitting unit 33A can absorb higher-energy radiation (X-rays) by including the GOS phosphor. This is because the GOS phosphor has a larger atomic number than the columnar crystal phosphor. This configuration is effective when the tube voltage of the radiation source 140 is changed between moving image shooting and still image shooting to increase the tube voltage during still image shooting in order to obtain a high-contrast still image. In addition, since the columnar crystal phosphor has high sensitivity to radiation, the dose of radiation during moving image shooting can be reduced and patient exposure can be reduced by using the columnar crystal phosphor for the second light emitting unit 33B. .
  • the GOS phosphor is composed of the first light detecting unit 32 and the second light emitting unit 33B. It is formed by applying or bonding to one of the light detection portions 34.
  • the columnar crystal phosphor is formed by vapor deposition or bonding to the other of the first light detection unit 32 and the second light detection unit 34.
  • the vapor deposition of the columnar crystal phosphor includes direct vapor deposition and indirect vapor deposition.
  • Indirect vapor deposition is a method in which a columnar crystal phosphor is deposited on a deposition substrate, the columnar crystal phosphor is bonded to the first light detection unit 32 or the second light detection unit 34, and then the deposition substrate is peeled off. .
  • the columnar crystal phosphor and the GOS phosphor are bonded together by bonding or by pouching in a state where both are pressed.
  • the columnar crystal phosphor may be directly or indirectly deposited on the GOS phosphor, and then the columnar crystal phosphor and the first light detection unit 32 or the second light detection unit 34 may be bonded together.
  • the first light emitting portion 33A is obtained by mixing a small particle GOS phosphor with a binder resin
  • the second light emitting portion 33B is obtained by mixing a large particle GOS phosphor with a binder resin. It may be used.
  • the large-particle GOS phosphor is inferior in resolution as compared with the small-particle GOS phosphor, but has high sensitivity to radiation, so that a highly sensitive moving image can be obtained.
  • a light reflecting layer may be provided between the first light emitting unit 33A and the second light emitting unit 33B.
  • the photoelectric conversion film 321C of the first light detection unit 32 is made of amorphous silicon, but the photoelectric conversion film 321C is made of an organic photoelectric conversion material. You may comprise with the material to contain. In this case, an absorption spectrum showing high absorption mainly in the visible light region is obtained, and the photoelectric conversion film 321C hardly absorbs electromagnetic waves other than visible light emitted from the scintillator 332. Thereby, the noise which generate
  • the photoelectric conversion film 321C made of an organic photoelectric conversion material can be formed by attaching an organic photoelectric conversion material onto the TFT substrate 32A using a droplet discharge head such as an ink jet head, and is included in the TFT substrate 32A.
  • the insulating substrate 325 is not required to have heat resistance. For this reason, the insulating substrate 325 can be made of a material other than glass.
  • the photoelectric conversion film 321 ⁇ / b> C is made of an organic photoelectric conversion material, radiation is hardly absorbed by the photoelectric conversion film 321 ⁇ / b> C, and thus attenuation of radiation due to transmission through the first light detection unit 32 is suppressed. Therefore, it is preferable that the photoelectric conversion film 321C is made of an organic photoelectric conversion material when the first radiation detector 40 is an ISS type.
  • the organic photoelectric conversion material that constitutes the photoelectric conversion film 321C is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the scintillator 332 in order to absorb the visible light emitted from the scintillator 332 most efficiently.
  • the absorption peak wavelength of the organic photoelectric conversion material matches the emission peak wavelength of the scintillator 332, but if the difference between the two is small, the visible light emitted from the scintillator 332 can be sufficiently absorbed. is there.
  • the difference between the absorption peak wavelength of the organic photoelectric conversion material and the emission peak wavelength of the scintillator 332 is preferably within 10 nm, and more preferably within 5 nm.
  • organic photoelectric conversion materials examples include quinacridone organic compounds and phthalocyanine organic compounds. Since the absorption peak wavelength in the visible region of quinacridone is 560 nm, if quinacridone is used as the organic photoelectric conversion material and CsI: Tl is used as the material of the scintillator 332, the difference in the peak wavelengths can be made within 5 nm. The amount of charge generated in the scintillator 332 can be substantially maximized.
  • the photoelectric conversion film 321C preferably contains an organic p-type compound or an organic n-type compound.
  • An organic p-type compound is a donor organic semiconductor typified by a hole-transporting organic compound and has a property of easily donating electrons. More specifically, the organic p-type compound is an organic compound having a smaller ionization potential when two organic materials are used in contact with each other. Any organic compound can be used as the donor organic semiconductor as long as it has an electron donating property.
  • the organic n-type compound is an acceptor organic semiconductor mainly represented by an electron transporting organic compound, and has a property of easily accepting electrons. More specifically, the organic n-type compound is an organic compound having a higher electron affinity when two organic compounds are used in contact with each other. As the acceptor organic semiconductor, any organic compound can be used as long as it has an electron accepting property.
  • the photoelectric conversion unit 321 only needs to include at least the electrodes 321A and 321B and the photoelectric conversion film 321C, but in order to suppress an increase in dark current, at least one of an electron blocking film and a hole blocking film is provided. It is preferable to provide both.
  • the active layer of the TFT 322 is preferably an amorphous oxide containing at least one of In, Ga, and Zn (for example, an In—O system), and at least two of In, Ga, and Zn are used.
  • Amorphous oxides containing for example, In—Zn—O, In—Ga—O, and Ga—Zn—O
  • amorphous oxides including In, Ga, and Zn are particularly preferable.
  • the active layer of the TFT 322 may be formed of an organic semiconductor material.
  • the organic semiconductor material include phthalocyanine compounds described in JP2009-212389A, pentacene, vanadyl phthalocyanine, and the like.
  • the active layer of the TFT 322 is formed of an amorphous oxide or an organic semiconductor material, it does not absorb radiation such as X-rays, or even if it is absorbed, the amount of noise remains very small.
  • the active layer of the TFT 322 may be formed of carbon nanotubes.
  • the switching speed of the TFT 322 is increased.
  • the degree of light absorption in the visible light region in the TFT 322 can be reduced.
  • the active layer is formed of carbon nanotubes, the performance of the TFT 322 is remarkably deteriorated just by mixing a very small amount of metallic impurities into the active layer. Therefore, the highly pure carbon nanotubes are separated and extracted by centrifugation or the like. Therefore, it must be used for forming the active layer.
  • the insulating substrate 325 is not limited to a substrate having high heat resistance such as a quartz substrate or a glass substrate, and a flexible substrate made of synthetic resin, aramid, or bionanofiber can be used.
  • flexible materials such as polyesters such as polyethylene terephthalate, polybutylene phthalate, and polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, and poly (chlorotrifluoroethylene).
  • a conductive substrate can be used. If such a flexible substrate made of a synthetic resin is used, the weight can be reduced.
  • the insulating substrate 325 includes an insulating layer for ensuring insulation, a gas barrier layer for preventing permeation of moisture and oxygen, an undercoat layer for improving flatness or adhesion to electrodes, and the like. May be provided.
  • the bio-nanofiber is a composite of a cellulose microfibril bundle (bacterial cellulose) produced by bacteria (Acetobacter Xylinum) and a transparent resin.
  • the cellulose microfibril bundle has a width of 50 nm and a size of 1/10 of the visible light wavelength, and has high strength, high elasticity, and low thermal expansion.
  • a transparent resin such as acrylic resin or epoxy resin in bacterial cellulose
  • a bio-nanofiber having a light transmittance of about 90% at a wavelength of 500 nm can be obtained while containing 60 to 70% of the fiber.
  • Bionanofiber has a low coefficient of thermal expansion (3-7ppm) comparable to silicon crystals, and is as strong as steel (460MPa), highly elastic (30GPa), and flexible. Thinner.
  • the first radiation detector 40, the second radiation detector 41, and the radiation dose measuring unit 42 all convert radiation into visible light with a scintillator, and convert this visible light into electric charge.
  • it may be a direct conversion type radiation detector that directly converts radiation into electric charges by a photoconductive layer such as amorphous selenium.
  • the radiation dose measurement sensor 31 is arrange
  • the cassette control unit 70 sets the readout region RA based on the position information of the radiation generator 14 detected by the position detection device 143 during moving image shooting.
  • One radiation detector 40 is caused to perform an imaging operation intermittently, a radiation irradiation area is detected from image data obtained by the first radiation detector 40, and a readout area RA is set in accordance with the position of this radiation irradiation area May be.
  • the readout region RA may be set so as to follow the progress of an insert such as a catheter inserted into a patient.
  • the read area RA is set by selecting the drive circuit 62A and the processing circuit 63A to be “Enable”.
  • the present invention is not limited to this, and is described in JP-A-8-47491.
  • the read area RA may be set by selecting a gate line and a data line using a RAM or a switching element.
  • the first radiation detector 40 is used for still image shooting
  • the second radiation detector 41 is used for moving image shooting.
  • the first radiation detector 40 is used for moving image shooting.
  • the second radiation detector 41 for photographing may be used for photographing a still image. In this case, only the region of interest can be locally imaged with the second radiation detector 41 while the first radiation detector 40 captures a wide range of moving images.
  • the electronic cassette is exemplified as the radiation imaging apparatus, but the present invention can be applied to a radiation detection apparatus such as a mammography apparatus instead of the electronic cassette.

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  • Physics & Mathematics (AREA)
  • Radiology & Medical Imaging (AREA)
  • Surgery (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
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  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
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  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • General Physics & Mathematics (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Measurement Of Radiation (AREA)
  • Radiography Using Non-Light Waves (AREA)

Abstract

Pour pouvoir effectuer rapidement une photographie fixe tout en opérant en imagerie vidéo, cette invention utilise une cassette électronique (15) équipée d'un premier détecteur de rayonnement (40) et d'un second détecteur de rayonnement (41). Le premier détecteur de rayonnement (40) comprend une partie électroluminescente (33) qui absorbe le rayonnement et produit une lumière visible, et une première partie détection de lumière (32) qui détecte la lumière visible. Le second détecteur de rayonnement (41) comprend la partie électroluminescente (33), et une seconde partie détection de lumière (34) qui se trouve du côté opposé au côté d'entrée du rayonnement. La seconde partie détection de lumière (34) comporte une zone de lecture (RA) qui est configurée dans une zone de détection de rayonnement (DA), la configuration de la zone de lecture (RA) variant selon la position d'un générateur de rayonnement (14). Une unité de commande de cassette (70) pilote le premier détecteur de rayonnement (40) en mode photographie fixe, et pilote la zone de lecture (RA) du second détecteur de rayonnement (41) en mode imagerie vidéo.
PCT/JP2012/065714 2011-07-27 2012-06-20 Équipement radiographique Ceased WO2013015044A1 (fr)

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JP2011-164277 2011-07-27
JP2011164277A JP2014193191A (ja) 2011-07-27 2011-07-27 放射線撮影装置

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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH10284289A (ja) * 1996-12-20 1998-10-23 General Electric Co <Ge> Ｘ線システム
JP2003307569A (ja) * 2002-04-16 2003-10-31 Canon Inc 放射線撮影装置、放射線撮影方法、コンピュータプログラム及びコンピュータ読み取り可能な記録媒体
JP2011017683A (ja) * 2009-07-10 2011-01-27 Fujifilm Corp 放射線画像検出器及びその製造方法
JP2011022132A (ja) * 2009-06-17 2011-02-03 Fujifilm Corp 放射線検出装置及び放射線画像検出システム

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH10284289A (ja) * 1996-12-20 1998-10-23 General Electric Co <Ge> Ｘ線システム
JP2003307569A (ja) * 2002-04-16 2003-10-31 Canon Inc 放射線撮影装置、放射線撮影方法、コンピュータプログラム及びコンピュータ読み取り可能な記録媒体
JP2011022132A (ja) * 2009-06-17 2011-02-03 Fujifilm Corp 放射線検出装置及び放射線画像検出システム
JP2011017683A (ja) * 2009-07-10 2011-01-27 Fujifilm Corp 放射線画像検出器及びその製造方法

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