WO2013125325A1 - Dispositif de radiographie, système de radiographie, procédé de commande de dispositif de radiographie, et programme de commande de dispositif de radiographie - Google Patents

Dispositif de radiographie, système de radiographie, procédé de commande de dispositif de radiographie, et programme de commande de dispositif de radiographie Download PDF

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Publication number
WO2013125325A1
WO2013125325A1 PCT/JP2013/052255 JP2013052255W WO2013125325A1 WO 2013125325 A1 WO2013125325 A1 WO 2013125325A1 JP 2013052255 W JP2013052255 W JP 2013052255W WO 2013125325 A1 WO2013125325 A1 WO 2013125325A1
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Prior art keywords
charge
radiation
image
gate
moving image
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PCT/JP2013/052255
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English (en)
Japanese (ja)
Inventor
大田　恭義
西納　直行
中津川　晴康
岩切　直人
北野　浩一
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富士フイルム株式会社
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/48—Diagnostic techniques
    • A61B6/486—Diagnostic techniques involving generating temporal series of image data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
    • H04N25/40—Extracting pixel data from image sensors by controlling scanning circuits, e.g. by modifying the number of pixels sampled or to be sampled
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
    • H04N25/60—Noise processing, e.g. detecting, correcting, reducing or removing noise
    • H04N25/62—Detection or reduction of noise due to excess charges produced by the exposure, e.g. smear, blooming, ghost image, crosstalk or leakage between pixels
    • H04N25/626—Reduction of noise due to residual charges remaining after image readout, e.g. to remove ghost images or afterimages
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
    • H04N25/70—SSIS architectures; Circuits associated therewith
    • H04N25/76—Addressed sensors, e.g. MOS or CMOS sensors
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N5/00—Details of television systems
    • H04N5/30—Transforming light or analogous information into electric information
    • H04N5/32—Transforming X-rays

Definitions

  • the present invention relates to a radiographic imaging apparatus, a radiographic imaging system, a radiographic imaging apparatus control method, and a radiographic imaging apparatus control program.
  • the present invention relates to a radiographic image capturing apparatus, a radiographic image capturing system, a radiographic image capturing apparatus control method, and a radiographic image capturing apparatus control program capable of capturing a still image and a moving image.
  • a radiographic image capturing apparatus that detects radiation irradiated from a radiation irradiation apparatus and transmitted through a subject with a radiation detector is known.
  • a moving image is taken by the radiographic image capturing apparatus to continuously shoot a plurality of radiographic images (still images).
  • Japanese Patent Application Laid-Open No. 2004-80514 describes a technique for controlling a gate voltage to be smaller than that in a high-dose imaging mode in a fluoroscopic mode in which moving image shooting is performed. It is described that there is a tendency to increase afterimages and increase afterimages.
  • the present invention provides a radiographic image capturing apparatus, a radiographic image capturing system, a radiographic image capturing apparatus control method, and a radiographic image capturing apparatus control program capable of capturing a moving image that can be interpreted as a smooth moving image. To do.
  • a first aspect of the present invention is a radiographic imaging apparatus including a sensor unit that generates electric charge according to irradiated radiation, and a switching element for reading out electric charge generated by the sensor unit.
  • a sensor unit that generates electric charge according to irradiated radiation
  • a switching element for reading out electric charge generated by the sensor unit.
  • the predetermined range of the radiographic apparatus is a range of 1/100 to 1/2 of the read charge amount.
  • control unit of the radiographic image capturing device includes an on period in which the switching element is turned on, and a voltage applied to turn on the switching element. By controlling at least one of them, the amount of charge read from the sensor unit is controlled.
  • control means of the radiographic imaging apparatus performs control so that the ON period is shortened as the temperature of the radiation detector increases.
  • control unit of the radiographic imaging device applies the switching element to turn on as the temperature of the radiation detector increases. Reduce the voltage to be applied.
  • the radiographic imaging device is provided corresponding to each pixel of the radiation detector, and the charge of an integrating capacitor for integrating the charge generated by the sensor unit is obtained.
  • a reset means for resetting is provided, and includes an amplifying means for amplifying an electric signal due to the electric charge read out from the corresponding pixel by the switching element at a predetermined amplification factor. By controlling the reset means, a part of the electric charge accumulated by being integrated in the integrating capacitor of the amplifying means is left unread within a predetermined range.
  • the control means of the radiographic image capturing apparatus controls the reading of electric charges when the frame rate in moving image capturing is equal to or less than a predetermined threshold.
  • control unit of the radiographic image capturing apparatus is configured based on an instruction from the user regarding the charge amount of the remaining charge.
  • the readout of the charge is controlled to leave the charge of the designated charge amount.
  • control means of the radiographic image capturing apparatus performs control so that the remaining charge amount differs according to at least one of the type of moving image capturing and the frame rate.
  • control means of the radiographic image capturing apparatus is configured such that the dose of radiation applied to the radiation detector is predetermined as a moving image capturing dose condition. If the condition is satisfied, the charge readout is controlled.
  • An eleventh aspect of the present invention is a radiographic imaging system comprising a radiation irradiating apparatus and the radiographic image capturing apparatus of the present invention for detecting radiation irradiated from the radiation irradiating apparatus.
  • a twelfth aspect of the present invention is a method for controlling a radiographic imaging apparatus, comprising: a sensor unit that generates a charge corresponding to the irradiated radiation; and a switching element for reading out the charge generated by the sensor unit.
  • a plurality of pixels configured in a matrix, and a step of taking a moving image using a radiation detector that detects a radiation image indicated by radiation, and a sensor unit generates and accumulates the moving image during shooting.
  • the charges generated by the sensor unit in the next frame shooting are further reduced. And a step of accumulating.
  • a control program for a radiographic imaging apparatus comprising: a sensor unit that generates a charge corresponding to the irradiated radiation; and a switching element for reading the charge generated by the sensor unit.
  • the sensor unit In the case where a plurality of pixels configured in the above are provided in a matrix and a moving image is captured using a radiation detector that detects a radiation image indicated by radiation, the sensor unit generates and accumulates the radiation image. Control to read out charges, leave a part of the charges unread within a predetermined range, and accumulate the charges generated by the sensor unit in the next frame shooting while the unread charges are accumulated And a means for controlling the computer as a control means of the radiographic image capturing apparatus.
  • FIG. 1 is a schematic configuration diagram of an outline of an overall configuration of an example of a radiographic imaging system according to the present embodiment. It is the schematic which shows the outline of the cross section of an example of the indirect conversion type radiation detector which concerns on this Embodiment. It is the schematic which shows the outline of the cross section of an example of the direct conversion type radiation detector which concerns on this Embodiment. It is a schematic circuit block diagram of an example of the electronic cassette concerning this Embodiment. It is a schematic block diagram of an example of the signal processing part which concerns on this Embodiment. It is a functional block diagram of an example of composition corresponding to a function of a cassette control part in an electronic cassette concerning this embodiment.
  • FIG. 1 shows a schematic configuration diagram of an overall configuration of an example of a radiographic imaging system according to the present exemplary embodiment.
  • the radiographic image capturing system 10 of the present embodiment can capture still images in addition to moving images.
  • “radiation image” refers to both a moving image and a still image unless otherwise specified.
  • a moving image refers to displaying still images one after another at a high speed and recognizing them as moving images.
  • the still image is shot, converted into an electric signal, transmitted, and the still image is transferred from the electric signal.
  • the process of replaying is repeated at high speed.
  • the moving image includes so-called “frame advance” in which the same area (part or all) is photographed a plurality of times within a predetermined time and continuously reproduced according to the degree of “high speed”. Shall be.
  • the radiographic imaging system 10 of the present exemplary embodiment is based on an instruction (imaging menu) input from an external system (for example, RIS: Radiology Information System: radiation information system) via the console 16. It has a function of taking a radiographic image by an operation such as the above.
  • an instruction for example, RIS: Radiology Information System: radiation information system
  • the radiographic image capturing system 10 of the present embodiment has a function of causing a doctor, a radiographer, or the like to interpret a radiographic image by displaying the captured radiographic image on the display 50 of the console 16 or the radiographic image interpretation device 18. Have.
  • the radiographic imaging system 10 includes a radiation generation device 12, a radiographic image processing device 14, a console 16, a storage unit 17, a radiographic image interpretation device 18, and an electronic cassette 20.
  • the radiation generator 12 includes a radiation irradiation control unit 22.
  • the radiation irradiation control unit 22 has a function of irradiating the imaging target region of the subject 30 on the imaging table 32 with the radiation X from the radiation irradiation source 22 ⁇ / b> A based on the control of the radiation control unit 62 of the radiation image processing apparatus 14. ing.
  • the radiation X transmitted through the subject 30 is applied to the electronic cassette 20 held in the holding unit 34 inside the imaging table 32.
  • the electronic cassette 20 has a function of generating charges according to the dose of the radiation X that has passed through the subject 30, generating image information indicating a radiation image based on the generated charge amount, and outputting the image information.
  • the electronic cassette 20 of this embodiment includes a radiation detector 26.
  • image information indicating a radiographic image output from the electronic cassette 20 is input to the console 16 via the radiographic image processing device 14.
  • the console 16 according to the present embodiment uses the radiography (LAN: Local Area Network) or the like from an external system (RIS) or the like, using a radiographing menu, various types of information, or the like. It has a function to perform control.
  • the console 16 according to the present embodiment has a function of transmitting / receiving various information including image information of a radiographic image to / from the radiographic image processing apparatus 14 and a function of transmitting / receiving various information to / from the electronic cassette 20. have.
  • the console 16 in the present embodiment is a server computer.
  • the console 16 includes a control unit 40, a display driver 48, a display 50, an operation input detection unit 52, an operation panel 54, an I / O unit 56, and an I / F unit 58.
  • the control unit 40 has a function of controlling the operation of the entire console 16.
  • the control unit 40 includes a CPU, a ROM, a RAM, and an HDD.
  • the CPU has a function of controlling the operation of the entire console 16.
  • Various programs including a control program used by the CPU are stored in advance in the ROM.
  • the RAM has a function of temporarily storing various data.
  • An HDD Hard Disk Drive
  • the display driver 48 has a function of controlling display of various information on the display 50.
  • the display 50 according to the present embodiment has a function of displaying an imaging menu, a captured radiographic image, and the like.
  • the operation input detection unit 52 has a function of detecting an operation state with respect to the operation panel 54.
  • the operation panel 54 is used by a doctor, a radiographer, or the like to input operation instructions related to radiographic image capturing.
  • the operation panel 54 includes, for example, a touch panel, a touch pen, a plurality of keys, a mouse, and the like. In addition, when it is set as a touch panel, it is good also as the display 50.
  • the I / O unit 56 and the I / F unit 58 transmit and receive various types of information to and from the radiographic image processing apparatus 14 and the radiation generating apparatus 12 through wireless communication, and also perform image information with the electronic cassette 20. And the like.
  • the control unit 40, the display driver 48, the operation input detection unit 52, and the I / O unit 56 are connected to each other via a bus 59 such as a system bus or a control bus so that information can be exchanged. Therefore, the control unit 40 controls the display of various information on the display 50 via the display driver 48 and controls the transmission / reception of various information with the radiation generator 12 and the electronic cassette 20 via the I / F unit 58. Each can be done.
  • the radiation image processing apparatus 14 has a function of controlling the radiation generation apparatus 12 and the electronic cassette 20 based on an instruction from the console 16.
  • the radiographic image processing device 14 has a function of controlling storage of the radiographic image received from the electronic cassette 20 in the storage unit 17 and display on the display 50 of the console 16 and the radiographic image interpretation device 18.
  • the radiation image processing apparatus 14 includes a system control unit 60, a radiation control unit 62, a panel control unit 64, an image processing control unit 66, and an I / F unit 68.
  • the system control unit 60 has a function of controlling the entire radiographic image processing apparatus 14 and a function of controlling the radiographic image capturing system 10.
  • the system control unit 60 includes a CPU, ROM, RAM, and HDD.
  • the CPU has a function of controlling operations of the entire radiographic image processing apparatus 14 and the radiographic image capturing system 10.
  • Various programs including a control program used by the CPU are stored in advance in the ROM.
  • the RAM has a function of temporarily storing various data.
  • the HDD has a function of storing and holding various data.
  • the radiation control unit 62 has a function of controlling the radiation irradiation control unit 22 of the radiation generator 12 based on an instruction from the console 16.
  • the panel control unit 64 has a function of receiving information from the electronic cassette 20 wirelessly or by wire.
  • the image processing control unit 66 has a function of performing various image processing on the radiation image.
  • the system control unit 60, the radiation control unit 62, the panel control unit 64, and the image processing control unit 66 are connected to each other through a bus 69 such as a system bus or a control bus so as to be able to exchange information.
  • the storage unit 17 of the present embodiment has a function of storing a captured radiographic image and information related to the radiographic image.
  • An example of the storage unit 17 is an HDD.
  • the radiological image interpretation apparatus 18 of the present embodiment is an apparatus having a function for an interpreter such as a doctor or a radiographer to interpret a captured radiographic image.
  • the radiographic image interpretation apparatus 18 is not specifically limited, What is called an image interpretation viewer, a console, a tablet terminal, etc. are mentioned.
  • the radiographic image interpretation apparatus 18 of the present embodiment is a personal computer. Similar to the console 16 and the radiographic image processing apparatus 14, the radiographic image interpretation apparatus 18 includes a CPU, ROM, RAM, HDD, display driver, display 23, operation input detection unit, operation panel 24, I / O unit, and I / O unit. F section is provided. In FIG. 1, only the display 23 and the operation panel 24 are shown, and other descriptions are omitted in order to avoid complicated description.
  • the radiation detector 26 provided in the electronic cassette 20 will be described.
  • the radiation detector 26 of the present embodiment includes a TFT substrate.
  • FIG. 2 a schematic cross-sectional view of an example of the indirect conversion type radiation detector 26 is shown in FIG.
  • the radiation detector 26 shown in FIG. 2 includes a TFT substrate and a radiation conversion layer.
  • the bias electrode 72 has a function of applying a bias voltage to the radiation conversion layer 74.
  • a positive bias voltage is supplied to the bias electrode 72 from a high voltage power supply (not shown).
  • a negative bias voltage is supplied to the bias electrode 72.
  • the radiation conversion layer 74 is a scintillator, and is formed so as to be laminated between the bias electrode 72 and the upper electrode 82 via the transparent insulating film 80 in the radiation detector 26 of the present embodiment.
  • the radiation conversion layer 74 is formed by forming a phosphor that emits light by converting the radiation X incident from above or below into light. Providing such a radiation conversion layer 74 absorbs the radiation X and emits light.
  • the wavelength range of light emitted from the radiation conversion layer 74 is preferably a visible light range (wavelength 360 nm to 830 nm). In order to enable monochrome imaging by the radiation detector 26, it is more preferable to include a green wavelength region.
  • a scintillator that generates fluorescence having a relatively wide wavelength region that can generate light in a wavelength region that can be absorbed by the TFT substrate 70 is desirable.
  • Examples of such a scintillator include CsI: Na, CaWO 4 , YTaO 4 : Nb, BaFX: Eu (X is Br or Cl), LaOBr: Tm, and GOS.
  • CsI cesium iodide
  • CsI Tl (cesium iodide to which thallium is added) or CsI: Na having an emission spectrum at the time of X-ray irradiation of 400 to 700 nm.
  • the emission peak wavelength in the visible light region of CsI: Tl is 565 nm.
  • the scintillator containing CsI it is preferable to use what was formed as a strip-shaped columnar crystal structure by the vacuum evaporation method.
  • the upper electrode 82 is preferably made of a conductive material that is transparent at least with respect to the emission wavelength of the radiation conversion layer 74 because light generated by the radiation conversion layer 74 needs to enter the photoelectric conversion film 86. Specifically, it is preferable to use a transparent conductive oxide (TCO) having a high transmittance for visible light and a small resistance value. Although a metal thin film such as Au can be used as the upper electrode 82, the TCO is preferable because the resistance value tends to increase when the transmittance of 90% or more is obtained.
  • ITO, IZO, AZO, FTO are preferably used SnO 2, TiO 2, and ZnO 2 and the like can. ITO is most preferable from the viewpoint of process simplicity, low resistance, and transparency.
  • the upper electrode 82 may have a single configuration common to all pixels, or may be divided for each pixel.
  • the photoelectric conversion film 86 includes an organic photoelectric conversion material that absorbs light emitted from the radiation conversion layer 74 and generates charges.
  • the photoelectric conversion film 86 includes an organic photoelectric conversion material, absorbs light emitted from the radiation conversion layer 74, and generates electric charges according to the absorbed light.
  • the photoelectric conversion film 86 containing an organic photoelectric conversion material has a sharp absorption spectrum in the visible range. Therefore, electromagnetic waves other than light emission by the radiation conversion layer 74 are hardly absorbed by the photoelectric conversion film 86, and noise generated when the radiation X such as X-rays is absorbed by the photoelectric conversion film 86 is effectively suppressed. can do.
  • the organic photoelectric conversion material of the photoelectric conversion film 86 is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the radiation conversion layer 74 in order to absorb the light emitted from the radiation conversion layer 74 most efficiently.
  • the absorption peak wavelength of the organic photoelectric conversion material matches the emission peak wavelength of the radiation conversion layer 74, but if the difference between the two is small, the light emitted from the radiation conversion layer 74 is sufficiently absorbed. Is possible.
  • the difference between the absorption peak wavelength of the organic photoelectric conversion material and the emission peak wavelength with respect to the radiation X of the radiation conversion layer 74 is preferably within 10 nm, and more preferably within 5 nm.
  • organic photoelectric conversion materials that can satisfy such conditions include quinacridone-based organic compounds and phthalocyanine-based organic compounds.
  • quinacridone-based 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 radiation conversion layer 74, the difference in the peak wavelength may be within 5 nm. It becomes possible. As a result, the amount of charge generated in the photoelectric conversion film 86 can be substantially maximized.
  • the electron blocking film 88 can be provided between the lower electrode 90 and the photoelectric conversion film 86.
  • the electron blocking film 88 suppresses an increase in dark current caused by injection of electrons from the lower electrode 90 to the photoelectric conversion film 86 when a bias voltage is applied between the lower electrode 90 and the upper electrode 82. it can.
  • An electron donating organic material can be used for the electron blocking film 88.
  • the hole blocking film 84 can be provided between the photoelectric conversion film 86 and the upper electrode 82.
  • the hole blocking film 84 suppresses increase in dark current due to injection of holes from the upper electrode 82 to the photoelectric conversion film 86 when a bias voltage is applied between the lower electrode 90 and the upper electrode 82. be able to.
  • An electron-accepting organic material can be used for the hole blocking film 84.
  • a plurality of lower electrodes 90 are formed in a lattice shape (matrix shape) at intervals, and one lower electrode 90 corresponds to one pixel.
  • Each lower electrode 90 is connected to a field effect thin film transistor (hereinafter referred to simply as “TFT”) 98 and a storage capacitor 96 of the signal output unit 94.
  • TFT field effect thin film transistor
  • An insulating film 92 is interposed between the signal output unit 94 and the lower electrode 90.
  • the signal output unit 94 corresponds to the lower electrode 90, and is a storage capacitor 96 that stores the charge transferred to the lower electrode 90, and a switching element that converts the charge stored in the storage capacitor 96 into an electrical signal and outputs the electrical signal.
  • TFT 98 is formed.
  • the region where the storage capacitor 96 and the TFT 98 are formed has a portion overlapping the lower electrode 90 in plan view. In order to minimize the plane area of the radiation detector 26 (pixel), it is desirable that the region where the storage capacitor 96 and the TFT 98 are formed is completely covered by the lower electrode 90.
  • the radiation detector 26 includes a so-called back surface reading method (PSS (Pentration Side Sampling) method) and a so-called front surface reading method (ISS (Irradiation Side Sampling) method).
  • PSS Purration Side Sampling
  • ISS Immunation Side Sampling
  • FIG. 2 in the back side scanning method, radiation X is irradiated from the side on which the radiation conversion layer 74 is formed, and a radiation image is read by the TFT substrate 70 provided on the back side of the incident surface of the radiation X. It is a method.
  • the radiation detector 26 emits light more strongly on the upper surface side of the radiation conversion layer 74 when the back surface reading method is adopted.
  • the surface reading method is a method in which radiation X is irradiated from the TFT substrate 70 side and a radiation image is read by the TFT substrate 70 provided on the surface side of the incident surface of the radiation X.
  • the radiation detector 26 is of the surface reading type, the radiation X transmitted through the TFT substrate 70 enters the radiation conversion layer 74 and the TFT substrate 70 side of the radiation conversion layer 74 emits light more strongly. Electric charges are generated in the photoelectric conversion portion 87 of each pixel 100 provided on the TFT substrate 70 by the light generated in the radiation conversion layer 74. For this reason, the radiation detector 26 is closer to the emission position of the radiation conversion layer 74 with respect to the TFT substrate 70 when the front surface reading method is used than when the rear surface reading method is used. High resolution.
  • the radiation detector 26 may be a direct conversion type radiation detector 26 as shown in a schematic cross-sectional view of an example in FIG.
  • the radiation detector 26 shown in FIG. 3 also includes a TFT substrate 110 and a radiation conversion layer 118 as in the indirect conversion type described above.
  • the TFT substrate 110 has a function of collecting and reading (detecting) carriers (holes) that are charges generated in the radiation conversion layer 118.
  • the TFT substrate 110 includes an insulating substrate 122 and a signal output unit 124.
  • the radiation detector 26 is an electronic reading sensor, the TFT substrate 110 has a function of collecting and reading out electrons.
  • the insulating substrate 122 absorbs the radiation X in the radiation converting layer 118 and the radiation converting layer 76, the insulating substrate 122 has a low radiation X absorbability and is a flexible, electrically insulating thin substrate (about several tens of ⁇ m).
  • the substrate having a thickness of 1 is preferable.
  • the insulating substrate 122 is preferably made of synthetic resin, aramid, bionanofiber, or film glass (ultra thin glass) that can be wound into a roll.
  • the signal detection unit 85 includes a storage capacitor 126 that is a charge storage capacitor, a TFT 128 that is a switching element that converts the electric charge stored in the storage capacitor 126 into an electric signal, and the charge collecting electrode 121.
  • a plurality of charge collection electrodes 121 are formed in a lattice shape (matrix shape) at intervals, and one charge collection electrode 121 corresponds to one pixel. Each charge collecting electrode 121 is connected to the TFT 128 and the storage capacitor 126.
  • the storage capacitor 126 has a function of storing charges (holes) collected by the charge collection electrodes 121.
  • the charges accumulated in the respective storage capacitors 126 are read out by the TFT 128.
  • a radiographic image is taken by the TFT substrate 110.
  • the undercoat layer 120 is formed between the radiation conversion layer 118 and the TFT substrate 110.
  • the undercoat layer 120 preferably has a rectifying characteristic from the viewpoint of reducing dark current and leakage current. Therefore, the resistivity of the undercoat layer 120 is preferably 10 8 ⁇ cm or more, and the film thickness is preferably 0.01 ⁇ m to 10 ⁇ m.
  • the radiation conversion layer 118 is a photoelectric conversion layer that is a photoconductive material that absorbs the irradiated radiation X and generates positive and negative charges (electron-hole carrier pairs) according to the radiation X.
  • the radiation conversion layer 118 is preferably composed mainly of amorphous Se (a-Se).
  • the radiation conversion layer 118 includes Bi 2 MO 20 (M: Ti, Si, Ge), Bi 4 M 3 O 12 (M: Ti, Si, Ge), Bi 2 O 3 , BiMO 4 (M: Nb).
  • the radiation conversion layer 118 is preferably an amorphous material having high dark resistance, good photoconductivity against radiation irradiation, and capable of forming a large area film at a low temperature by a vacuum deposition method.
  • the thickness of the radiation conversion layer 118 is preferably in the range of 100 ⁇ m or more and 2000 ⁇ m or less in the case of a photoconductive substance containing a-Se as a main component as in the present embodiment, for example.
  • the range is preferably 100 ⁇ m or more and 250 ⁇ m or less.
  • it is preferably in the range of 500 ⁇ m or more and 1200 ⁇ m or less.
  • the electrode interface layer 116 has a function of blocking hole injection and a function of preventing crystallization.
  • the electrode interface layer 116 is formed between the radiation conversion layer 118 and the overcoat layer 114.
  • the electrode interface layer 116 is preferably an inorganic material such as CdS, CeO 2 , Ta 2 O 5 , and SiO, or an organic polymer.
  • the layer made of an inorganic material is preferably used by adjusting the carrier selectivity by changing the composition from the stoichiometric composition or by using a multi-component composition with two or more kinds of homologous elements.
  • an insulating polymer such as polycarbonate, polystyrene, polyimide, and polycycloolefin can be mixed with a low molecular weight electron transport material at a weight ratio of 5% to 80%.
  • electron transporting materials trinitrofluorene and derivatives thereof, diphenoquinone derivatives, bisnaphthyl quinone derivatives, oxazole derivatives, triazole derivatives, C 60 (fullerene), and those that have been mixed with carbon clusters C 70 etc. are preferred. Specific examples include TNF, DMDB, PBD, and TAZ.
  • a thin insulating polymer layer can also be preferably used.
  • the insulating polymer layer is preferably an acrylic resin such as parylene, polycarbonate, PVA, PVP, PVB, polyester resin, and polymethyl methacrylate.
  • the film thickness is preferably 2 ⁇ m or less, and more preferably 0.5 ⁇ m or less.
  • the overcoat layer 114 is formed between the electrode interface layer 116 and the bias electrode 112.
  • the overcoat layer 114 preferably has a rectifying characteristic from the viewpoint of reducing dark current and leakage current. Therefore, the resistivity of the overcoat layer 114 is preferably 10 8 ⁇ cm or more, and the film thickness is preferably 0.01 ⁇ m to 10 ⁇ m.
  • the bias electrode 112 is substantially the same as the bias electrode 72 in the direct conversion type described above, and has a function of applying a bias voltage to the radiation conversion layer 118.
  • the radiation detector 26 is not limited to that shown in FIGS. 2 and 3 and can be variously modified.
  • the signal output units (94, 124) with low possibility of arrival of radiation X are CMOS (ComplementaryarMetal-Oxide Semiconductor) images with low resistance to radiation X instead of the above-described ones.
  • CMOS ComplementaryarMetal-Oxide Semiconductor
  • You may combine TFT with other imaging elements, such as a sensor. Further, it may be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to the gate signal of the TFT.
  • CCD Charge-Coupled Device
  • a flexible substrate may be used.
  • the ultra-thin glass by the float method developed recently as a base material as a flexible substrate.
  • the ultra-thin glass that can be applied at this time, for example, “Asahi Glass Co., Ltd.,“ Successfully developed the world's thinnest 0.1 mm thick ultra-thin glass by the float method ”, [online], [2011 Aug. 20 search], Internet ⁇ URL: http://www.agc.com/news/2011/0516.pdf> ”.
  • FIG. 4 shows a schematic circuit configuration diagram of an example of the electronic cassette 20.
  • the electronic cassette 20 including the radiation detector 26 illustrated in FIG. 2 will be described as a specific example.
  • FIG. 4 shows a state in which the electronic cassette 20 is viewed in plan from the radiation X irradiation side. In FIG. 4, the radiation conversion layer 74 is not shown.
  • the electronic cassette 20 includes a cassette control unit 130, a gate line driver 132, a signal processing unit 134, and a plurality of pixels (in this embodiment, n pixels are arranged as a specific example) arranged in a matrix. 100.
  • the electronic cassette 20 includes a plurality of gate lines 136 along the row direction of the pixels 100 and a plurality of signal lines 138 along the column direction of the pixels 100. Each gate line 136 is connected to the gate line driver 132, and each signal line 138 is connected to the signal processing unit 134.
  • the electronic cassette 20 sequentially turns on the TFT 98 for each row, thereby converting the radiation X into fluorescence by the radiation conversion layer 74, converting the fluorescence from the fluorescence by the photoelectric conversion film 86 and storing the electric charge accumulated in the storage capacitor 96 into an electrical signal.
  • a gate-on voltage is sequentially applied to the gates of the TFTs 98 by sequentially outputting ON signals to the gate lines 136 in accordance with a predetermined frame rate (gate-on time) from the gate line driver 132, so that the TFTs 98 are sequentially turned on. Turns on.
  • an electrical signal corresponding to the charge accumulated in the storage capacitor 96 flows to the signal line 138, respectively.
  • FIG. 5 shows a schematic configuration diagram of an example of the signal processing unit 134.
  • the signal processing unit 134 amplifies the inflowed electric charge (analog electric signal) by the amplifier circuit 140 and then performs A / D conversion by the ADC (AD converter) 144, and converts the electric signal converted into the digital signal into the cassette control unit 130. Output to.
  • the amplifier circuit 140 is provided for each signal line 138. That is, the signal processing unit 134 includes a plurality of amplifier circuits 140 that are the same number as the signal lines 138 of the radiation detector 26.
  • the amplification circuit 140 is constituted by a charge amplifier circuit.
  • the amplifier circuit 140 includes an amplifier 142 such as an operational amplifier, a capacitor C connected in parallel to the amplifier 142, and a charge reset switch SW1 connected in parallel to the amplifier 142.
  • the charge is read out by the TFT 98 of the pixel 100 with the charge reset switch SW1 turned off, and the charge read out by the TFT 98 is accumulated in the capacitor C.
  • the voltage value output from 142 increases.
  • the cassette control unit 130 applies a charge reset signal to the charge reset switch SW1 to control on / off of the charge reset switch SW1.
  • the charge reset switch SW1 When the charge reset switch SW1 is turned on, the input side and output side of the amplifier 142 are short-circuited, and the capacitor C is discharged.
  • the ADC 144 has a function of converting an electrical signal, which is an analog signal input from the amplifier circuit 140, into a digital signal when the S / H (sample hold) switch SW is on.
  • the ADC 144 sequentially outputs the electrical signal converted into the digital signal to the cassette control unit 130.
  • the ADC 144 of this embodiment receives the electrical signals output from all the amplifier circuits 140 provided in the signal processing unit 134. That is, the signal processing unit 134 of the present embodiment includes one ADC 144 regardless of the number of amplifier circuits 140 (signal lines 138).
  • the cassette control unit 130 has a function of controlling the operation of the entire electronic cassette 20.
  • the cassette control unit 130 of the present embodiment has a function of controlling to generate residual charges when performing moving image shooting (details will be described later).
  • FIG. 6 shows a functional block diagram of an example of a configuration corresponding to the function of the cassette control unit 130 in the electronic cassette 20 of the present embodiment.
  • the cassette control unit 130 includes a CPU, ROM, RAM, and HDD.
  • the CPU has a function of controlling the operation of the entire electronic cassette 20.
  • Various programs including a control program used by the CPU are stored in advance in the ROM.
  • the RAM has a function of temporarily storing various data.
  • the HDD has a function of storing and holding various data.
  • the communication control unit 156 has a function of transmitting and receiving various types of information including image information of radiographic images to and from the radiographic image processing apparatus 14 and the console 16 by wireless communication or wired communication.
  • the temperature detection unit 154 has a function of detecting the temperature of the electronic cassette 20, more preferably the temperature of the radiation detector 26. The temperature detected by the temperature detection unit 154 is output to the cassette control unit 130.
  • the dose detection unit 155 has a function of detecting the dose of the radiation X irradiated to the electronic cassette 20.
  • the configuration of the dose detection unit 155 is not particularly limited, and the radiation X irradiated to the electronic cassette 20 is detected during a predetermined detection period, and the dose irradiated during the detection period is determined in advance. What is necessary is just to be able to compare with a threshold value.
  • the radiation detector 26 may be provided with detection pixels for detecting the radiation X, or some of the pixels 100 may be used as detection pixels. It may be used. Examples of such detection pixels include the pixel 100 including the shorted TFT 98, but are not limited thereto.
  • dose refers to a so-called mAs value obtained by multiplying the tube current (mA) when the radiation X is output and the irradiation time (sec).
  • the cassette control unit 130 controls the radiation detector 26 so as to capture a radiographic image based on an imaging menu including imaging conditions when the radiographic image received by the communication control unit 156 is captured. Further, the cassette control unit 130 performs control so that the charge according to whether the radiographic image to be captured is a still image or a moving image, the frame rate, the type of moving image, the temperature detected by the temperature detecting unit 154, or the like remains. To do.
  • the captured still images of multiple frames are displayed in succession.
  • the image can be interpreted as a smooth image in which there is a connection between the plurality of frames.
  • the time resolution of the human eye is said to be about 50 ms to 100 ms. Flashing light shorter than this time (corresponding to a high frame rate) is perceived by humans as being continuously lit. For example, in the region where the commercial power supply frequency is 60 Hz, the light of the incandescent bulb blinks 120 times per second, but usually does not feel flickering (flashing). For these reasons, it is generally considered that the limit that humans can recognize as moving images is 10 fps to 20 fps.
  • the charge is read at a uniform rate with respect to the stored charge amount. That is, according to the read time, a predetermined proportion of charges are left unread and become residual charges. Since charges remain uniformly at a predetermined rate in this way, afterimages with a density corresponding to the density of the moving image (hereinafter referred to as “main image”) generated by the read charges (generated by the residual charges left unread) Afterimage) occurs.
  • main image a density corresponding to the density of the moving image
  • an afterimage generated by the residual charge left unread with respect to the main image causes movement between frame rates.
  • the afterimage is prevented from having such a density that an obstacle occurs in the observation and confirmation of the moving image.
  • the human eye recognizes an image with a log-transformed value (density).
  • the human eye recognizes the same in the radiographic image.
  • the afterimage density can be observed as a smooth image by setting the afterimage density generated by the residual charge left unread relative to the main image to be in the range of 1/100 or more and 1/2 or less. It is preferable for confirmation.
  • control is performed so that a part of the charge is left unread so that the charge remains at a predetermined ratio such that the density of the afterimage is in the range of 1/100 or more and 1/2 or less.
  • the amount of unread charges corresponds to the density of the afterimage. Therefore, in this embodiment, control is performed so that the residual charge amount is in the range of 1/100 or more and 1/2 or less of the read charge amount.
  • whether or not an afterimage is generated is controlled according to the frame rate of the moving image.
  • the limit depends on the frame rate, and at least frames in the range from the frame rate (lower limit) that does not result in a smooth image without an afterimage to the frame rate (upper limit) that results in an afterimage in a range that does not hinder observation or confirmation.
  • the rate is controlled to generate an afterimage.
  • these frame rates are predetermined as threshold values and stored in the storage unit 150.
  • by setting a plurality of threshold values within the range from the lower limit frame rate to the upper limit frame rate afterimages are generated, for example, by actively utilizing afterimages at low frame rates.
  • a plurality of conditions may be provided in stages and controlled.
  • the gate on time of the TFT 98 can be shortened.
  • the gate-on time refers to a time for applying a gate-on voltage for turning on the gate of the TFT 98.
  • the amount of charge read from the storage capacitor 96 is reduced as in the case of shortening the gate-on time. As a result, all the charges stored in the storage capacitor 96 are not read out, but a part of them are left unread and become residual charges.
  • which method is used is not particularly limited.
  • control process is performed by executing a control process control program by the CPU of the cassette control unit 130.
  • control program is stored in advance in the ROM of the cassette control unit 130, the storage unit 150, or the like, but may be downloaded from an external system (RIS), a CD-ROM, a USB, or the like. Good.
  • step S100 it is determined whether the radiographic image instructed to be captured is a moving image or a still image.
  • the method for determining whether the image is a still image or a moving image is, for example, when information indicating either a still image or a moving image is included in the imaging menu instructed from the radiation image processing device 14 or the console 16 or the like. The determination may be made based on the information.
  • the dose of radiation X irradiated when shooting a moving image is often different from the dose of radiation X irradiated when shooting a still image.
  • the dose per frame one frame may be reduced in order to avoid an increase in the exposure dose of the subject 30.
  • the dose may be smaller than that in the case of a still image.
  • the dose may be higher than in the case of a still image.
  • the dose irradiated to the electronic cassette 20 (subject 30) during a predetermined period differs between the still image and the moving image. Therefore, as a determination method, a threshold is set in advance based on a dose regarded as a moving image or a dose regarded as a still image, and the dose of the radiation X detected by the dose detection unit 155 is compared with the threshold. It may be determined whether or not.
  • step S100 determines whether the image is a still image. If it is determined in step S100 that the image is a still image, the determination is negative and the process proceeds to step S102.
  • step S102 when irradiation with radiation X is started from the radiation irradiation source 22A, imaging is started. Note that the start of imaging may be determined based on an instruction from the radiation image processing apparatus 14, the console 16, or the like. Further, as described above, the radiation dose detected by detecting the radiation X on the electronic cassette 20 side is compared with the threshold value for detecting the start of irradiation, and when the detected radiation dose exceeds the threshold value, the start of imaging is performed. It may be considered.
  • control in photographing is performed so that charges are read out from the pixel 100 by the gate-on time T and the gate-on voltage V for still images.
  • the cassette control unit 130 sends the gate signal indicating the gate voltage V to the gate line 136 (TFT 98) to the gate line driver 132 so as to output the gate signal V to the gate line 136 (TFT 98).
  • Output a control signal.
  • a time chart in the case of still image shooting is shown in FIG.
  • the readout period in which the charge accumulated in the accumulation capacitor 96 is read out.
  • the accumulation period is not shown, and only the read period is shown.
  • a gate signal for turning on the gate of the TFT 98 is sequentially output from the gate line driver 132 to the gate line 136 from the first line to the n-th line.
  • the gate voltage V is applied, the charge is read from the pixel 100 during the gate on time T, and the charge is output to the signal line 138, and an electric signal flows through the signal line 138.
  • the charge output to the signal line 138 is sampled by the amplifier 142 of the amplifier circuit 140 according to the amplifier sampling period. Also, the sampled charge is reset.
  • the gate off time refers to the time from when the TFT 98 is turned off until the TFT 98 of the next line is turned on. Note that in the case of shooting a plurality of frames, after the shooting of the first picture, after shifting to an accumulation period for the next shooting, the readout period shown in FIG. In the electronic cassette 20 of the present embodiment, when the number of shots instructed by the shooting menu is finished in this way, the present processing is finished.
  • step S100 determines whether it is a moving image.
  • step S106 it is determined whether the frame rate is 15 fps based on the shooting menu.
  • the frame rate is 15 fps or less.
  • reading is controlled so that charges remain.
  • the frame rate is not limited to other values.
  • an interpreter of a captured moving image may be able to set the frame rate. Note that the correspondence between the frame rate, the gate-on time, and the gate-on voltage is stored in the storage unit 150 in advance.
  • step S106 If it is determined in step S106 that the frame rate is not 15 fps or less, the process proceeds to step S108, where the gate-on voltage v0 is acquired from the stored correspondence. In the next step S110, after acquiring the gate-on time t0 from the stored correspondence, the process proceeds to step S116.
  • the gate-on voltage and the gate-on time are the same as those for still image shooting so as not to unread the charges.
  • step S106 determines whether it is 15 fps or less. If it is determined in step S106 that it is 15 fps or less, the process proceeds to step S112, where the gate-on voltage v1 is acquired from the stored relationship. In the next step S114, the gate-on time t1 is acquired from the stored correspondence, and the process proceeds to step S116.
  • step S116 imaging is started when radiation X irradiation is started from the radiation source 22A, as in step S102.
  • step S118 charges are read out based on the acquired gate-on voltage and gate-on time.
  • a time chart in this case is shown in FIG. In FIG. 9, the accumulation period of each frame is not shown, and only the readout period is shown.
  • a gate signal for turning on the gate of the TFT 98 is sequentially output from the gate line driver 132 to the gate line 136 from the first line to the n-th line.
  • shooting is performed at a frame rate with a gate-on voltage v1 and a gate-on time t1. Note that in the case of shooting a plurality of frames, after the shooting of the first frame, after shifting to an accumulation period for the next shooting, the readout period shown in FIG.
  • step S120 it is determined whether or not to end the shooting. If the shooting of all frames has not been completed yet, the determination is negative and the process returns to step S118 to repeat this process. On the other hand, when the shooting of all the frames is completed, or when the shooting of a series of moving images instructed to be shot is completed, the process is ended in affirmative.
  • FIG. 10 shows an example of a flowchart of the control process.
  • steps that are substantially the same as the basic control processing shown in FIG. 7 are denoted by the same step numbers, description thereof is omitted here, and different processing is described.
  • each mode is classified into two types (modes): a mode for high image quality and a mode for smooth images. Control for each mode.
  • the correspondence relationship between the mode and the above-described moving image shooting type (condition) is stored in the storage unit 150 in advance.
  • the storage unit 150 further stores a gate-on voltage and a gate-on time for each mode.
  • step S101 is provided instead of step S106 shown in FIG.
  • step S108 the process proceeds to step S112.
  • moving image shooting is performed in which charges are left unread so that a smooth image is obtained. It can be carried out.
  • FIG. 11 shows an example of a flowchart of the control process.
  • steps that are substantially the same as the basic control processing shown in FIG. 7 are denoted by the same step numbers, description thereof is omitted here, and different processing is described.
  • FIG. 12 shows the relationship among temperature, current for turning on the TFT 98 (gate on current), and leakage current.
  • the gate-on current increases as the temperature increases.
  • the gate-on current is large, the charge can be easily read. For this reason, the higher the temperature, the harder the charge remains, so the gate on time of the TFT 98 is lengthened. Note that it is preferable to shorten the gate-on time from the viewpoint of suppressing the discharge of dark charges.
  • FIG. 13 shows a schematic diagram of the gate-on current.
  • the gate-on current shows an attenuation curve as shown in FIG. Since the slow decay component is the charge read from the shallow trap, it is considered that the contribution of dark charge is large.
  • the attenuation can be cut and the contribution of the dark charge component can be reduced.
  • the higher the gate-on voltage of the TFT 98 the easier it is to read out the charge and the less the residual charge. Therefore, in the control process shown in FIG. 11, the gate-on voltage is decreased as the temperature is higher.
  • the radiation detector 26 is controlled to perform imaging with a gate-on voltage and a gate-on time corresponding to the temperature acquired from the temperature detection unit 154. Note that the relationship between the temperature, the gate-on time, and the change frequency is stored in the storage unit 150 in advance.
  • step S105 is provided before the process proceeds to step S106 when it is determined (affirmed) that it is a moving image in step S100.
  • step S105 the detected temperature is acquired from the temperature detection unit 154.
  • step S109 and step S111 are provided in place of step S108 and step S110 shown in FIG.
  • step S109 a gate-on v0 voltage corresponding to the acquired temperature is acquired.
  • step S111 the gate on time t0 corresponding to the acquired temperature is acquired.
  • step S113 and step S115 are provided in place of step S112 and step S114 shown in FIG.
  • step S113 the gate-on voltage v1 corresponding to the acquired temperature is acquired.
  • step S115 the gate on time t1 corresponding to the acquired temperature is acquired.
  • moving images are captured with a gate-on voltage and a gate-on time corresponding to the temperature of the radiation detector 26, so that an image can be displayed more smoothly.
  • FIG. 14 shows an example of a flowchart of the control process.
  • steps that are substantially the same as the basic control processing shown in FIG. 7 are denoted by the same step numbers, description thereof is omitted here, and different processing is described.
  • the afterimage instruction is an afterimage density, but is not limited to the density itself.
  • the user may give an instruction using the operation panel 54 of the console 16 or the operation panel 24 of the radiographic image interpretation apparatus 18.
  • a predetermined moving image having afterimages corresponding to a plurality of predetermined densities (residual charge amounts) may be displayed on the display 50 of the console 16, the display 23 of the radiographic image interpretation device 18, or the like. With this display, the user may select and indicate a moving image including a desired afterimage from among the displayed predetermined moving images.
  • step S107-1 is provided after step S100 instead of step S106 shown in FIG. Further, in this control process, steps S107-2 and S107-3 are provided instead of steps S112 and S114 shown in FIG.
  • step S107-1 it is determined whether or not there is an instruction regarding an afterimage. As described above, in step S107-1, it is determined whether or not there has been an instruction regarding an afterimage from the user as described above. If there is no instruction regarding the afterimage, the process proceeds to step S108, and the same processing as described above is performed. On the other hand, if there is an instruction regarding an afterimage, the process proceeds to step S107-2 to acquire an instruction regarding an afterimage.
  • the storage unit 150 stores in advance the gate-on voltage vx and the gate-on time tx for each instruction related to each afterimage. For example, as described above, when the user selects and instructs a moving image including a desired afterimage, the gate-on voltage vx and the gate-on time tx are stored for each predetermined moving image. When only one of the gate-on voltage vx and the gate-on time tx is controlled and one of them is set to a fixed value, only one to be controlled may be stored for each predetermined moving image.
  • step S118 subsequent to step S116, the charge is read by the gate-on voltage vx and the gate-on time tx according to the instruction regarding the afterimage.
  • the user when a user interprets a moving image taken in real time during shooting after the start of moving image shooting, the user becomes a desired image (for example, an image having no sense of incongruity due to an afterimage) while watching the moving image.
  • the density of the afterimage may be adjusted.
  • a method similar to the above-described instruction regarding an afterimage by the user may be used.
  • the frame rate and the type of moving image are set so that the motion between the frames is interpreted as a smooth image so that the motion between the frames looks smooth. Accordingly, the gate-on voltage of the TFT 98 of each pixel 100 is reduced and the gate-on time is shortened as compared with still image shooting.
  • the gate-on voltage v0 and the gate-on time t0 are the same as those for still image shooting.
  • the gate-on voltage v1 (v0> v1) and the gate-on time t1 (t0> t1) are used.
  • the charge is left so that the density of the afterimage is in the range of 1/100 or more and 1/2 or less with respect to the density of the main image.
  • the electronic cassette 20 of the present embodiment can perform moving image shooting that can be interpreted as a smooth moving image.
  • a TFT 98 for reading out charge from the storage capacitor 96 of the pixel 100 as shown in FIGS. 8 and 9, a TFT whose gate is turned on when a positive gate-on voltage is applied is used.
  • a TFT that turns on when a negative gate-on voltage is applied may be used.
  • “large” and “small” of the gate-on voltage mean that the amplitude of the voltage is “large” and “small”, respectively, and that the absolute value of the voltage value is “large” and “small”.
  • the cassette control unit 130 functions to perform the above-described control processing.
  • the present invention is not limited to this.
  • the radiographic image processing device 14 or the console 16 performs the above-described control processing.
  • An instruction may be output to the gate line driver 132 via the cassette control unit 130.
  • the shape of the pixel 100 is not limited to the present embodiment.
  • the rectangular pixel 100 is shown in FIG. 4, but the shape of the pixel 100 is not limited to the rectangular shape and may be other shapes.
  • the arrangement of the pixels 100 is not limited to this embodiment mode. For example, as a form in which the pixels 100 are arranged in a matrix, as shown in FIG. 4, a case where the pixels 100 are arranged in a rectangular shape with regularity is shown, but the pixels 100 are arranged in a two-dimensional manner. It will not be limited if it has a form arranged.
  • the arrangement of the gate lines 136 and the signal lines 138 may be such that the signal lines 138 are arranged in the row direction and the gate lines 136 are arranged in the column direction, contrary to the present embodiment.
  • the configuration of the radiographic imaging system 10, the electronic cassette 20, the radiation detector 26, and the like described in the present embodiment and the control processing are examples, and the situation is within the scope not departing from the gist of the present invention. Needless to say, it can be changed accordingly. For example, it goes without saying that the control processes shown in FIGS. 7, 10, and 11 may be used in combination.
  • the gate-on voltage and gate-on time of the TFT 98 of the pixel 100 are controlled so as to leave the charge in the pixel 100 unread, but the present invention is not limited to this.
  • the charge readout may be controlled by controlling the on-time of the charge reset switch SW1.
  • the charge reset switch is set so that the charge accumulated in the capacitor C of the amplifier circuit 140 is not discharged and discharged to the ADC 144 but remains in the capacitor C.
  • the charge readout may be controlled by controlling the ON time of SW1.
  • the radiation X described in the present embodiment is not particularly limited, and X-rays, ⁇ -rays, and the like can be applied.
  • Radiation Imaging System 20 Electronic Cassette 26 Radiation Detector 98, 128 TFT 100 pixels 130 cassette control unit 150 storage unit 154 temperature detection unit 155 dose detection unit

Abstract

La présente invention permet une interprétation par rayons X sous forme d'image animée à flux fluide. A savoir, lors de la réalisation d'une photographie d'image animée, la tension de marche de TFT de chaque pixel est rendue plus petite, et le temps de marche plus court, qu'une photographie d'image fixe, selon des cadences de trame et des types d'image animée, de telle sorte qu'un mouvement entre trames semble être fluide et est interprété par rayons X comme une image fluide. Spécifiquement, une charge est laissée non lue lorsqu'elle est dans une faible cadence de trame ou une image animée de positionnement, de telle sorte qu'une image après se produit afin qu'un mouvement entre trames semble fluide.
PCT/JP2013/052255 2012-02-23 2013-01-31 Dispositif de radiographie, système de radiographie, procédé de commande de dispositif de radiographie, et programme de commande de dispositif de radiographie WO2013125325A1 (fr)

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