WO2013136597A1 - Dispositif de commande de radiographie, système de radiographie, procédé de commande du dispositif de radiographie, et programme de commande de radiographie - Google Patents

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

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Publication number
WO2013136597A1
WO2013136597A1 PCT/JP2012/080094 JP2012080094W WO2013136597A1 WO 2013136597 A1 WO2013136597 A1 WO 2013136597A1 JP 2012080094 W JP2012080094 W JP 2012080094W WO 2013136597 A1 WO2013136597 A1 WO 2013136597A1
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conversion
conversion means
power consumption
case
predetermined
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PCT/JP2012/080094
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English (en)
Japanese (ja)
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西納　直行
岩切　直人
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富士フイルム株式会社
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    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
    • H01L27/00—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate
    • H01L27/14—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate including semiconductor components sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation
    • H01L27/144—Devices controlled by radiation
    • H01L27/146—Imager structures
    • H01L27/14601—Structural or functional details thereof
    • H01L27/14609—Pixel-elements with integrated switching, control, storage or amplification elements
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
    • H01L27/00—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate
    • H01L27/14—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate including semiconductor components sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation
    • H01L27/144—Devices controlled by radiation
    • H01L27/146—Imager structures
    • H01L27/14643—Photodiode arrays; MOS imagers
    • H01L27/14658—X-ray, gamma-ray or corpuscular radiation imagers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N23/00—Cameras or camera modules comprising electronic image sensors; Control thereof
    • H04N23/30—Cameras or camera modules comprising electronic image sensors; Control thereof for generating image signals from X-rays
    • 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
    • H04N25/42—Extracting pixel data from image sensors by controlling scanning circuits, e.g. by modifying the number of pixels sampled or to be sampled by switching between different modes of operation using different resolutions or aspect ratios, e.g. switching between interlaced and non-interlaced mode
    • 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
    • H04N25/78—Readout circuits for addressed sensors, e.g. output amplifiers or A/D converters

Definitions

  • the present invention relates to a radiographic imaging control device, a radiographic imaging system, a radiographic imaging device control method, and a radiographic imaging control program.
  • radiation detectors such as FPD (Flat Panel Detector) that can arrange radiation sensitive layers on TFT (Thin Film Transistor) active matrix substrates and convert radiation dose into digital data (electrical signals) (referred to as “electronic cassettes”)
  • FPD Fluor Deposition Detector
  • TFT Thin Film Transistor
  • electrospray cassettes a radiation image capturing apparatus that captures a radiation image represented by the amount of irradiated radiation using this radiation detector has been put into practical use.
  • the technique described in Japanese Patent Application Laid-Open No. 2010-88460 includes a plurality of multiplexers, and when some of the plurality of multiplexers are connected, the other multiplexers control the switches so as to perform precharge processing. Thus, it has been proposed to shorten the readout time.
  • the radiation detector is capable of shooting moving images such as fluoroscopic shooting in addition to still image shooting, and a technique described in Japanese Patent No. 343277 has been proposed as a technique related to a shooting mode.
  • an X-ray tube that exposes X-rays to a subject
  • a conversion unit that converts an X-ray transmission image that has passed through the subject into an optical image, and light into a charge signal
  • the signal charges are sequentially read out and output one by one in the imaging mode, and the signal charges of a plurality of imaging elements are simultaneously output in the fluoroscopic mode.
  • the selective operation between the high frame rate mode and the high definition mode is easily realized.
  • JP 2010-88460 A Japanese Patent No. 3431277 JP 2001-251557 A
  • serial conversion is performed using a multiplexer as in the techniques described in Japanese Patent Application Laid-Open No. 2010-88460 and Japanese Patent No. 3341277. Has been done.
  • the present invention has been made in consideration of the above-described facts, and is a radiographic imaging control device, a radiographic imaging system, a radiation that can achieve both a reduction in the transient response waiting time of the conversion means for serial conversion and a reduction in power consumption.
  • An image capturing apparatus control method and a radiation image capturing control program are provided.
  • a plurality of pixels configured to include 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 are arranged.
  • a plurality of charge signals by inputting respective charge signals held by a radiation detector and a plurality of holding means for holding a charge signal generated by each sensor unit of the radiation detector and read by the switching element
  • a plurality of conversion means for performing serial conversion by selecting and outputting one charge signal from, a switching means for switching the number of conversion means to be used, and a predetermined photographing or power consumption that requires high-speed reading In the case of predetermined conditions where reduction is not required, serial conversion is performed using a plurality of conversion means, and high-speed reading is not required in advance.
  • the number of conversion means to be used is smaller than that required when high-speed readout is required or when power consumption reduction is not required in the case of taking a picture or in a condition where power consumption reduction is required.
  • a plurality of pixels configured to include a sensor unit and a switching element are arranged, and charges corresponding to the irradiated radiation are generated in the sensor unit. The charge is read by the switching element.
  • Each of the plurality of conversion means serially converts each charge signal held by the plurality of holding means that holds the charge signal generated by each sensor unit of the radiation detector and read by the switching element.
  • the conversion means for example, a multiplexer that selects and outputs one signal from a plurality of input signals is applied.
  • the control means uses a plurality of conversion means in the case of a predetermined shooting that requires high-speed reading such as moving image shooting or a predetermined condition that does not require a reduction in power consumption.
  • the number of conversion means to be used when the switching means is controlled so as to perform conversion, and in the case of predetermined shooting that does not require high-speed readout such as still image shooting, or in the condition that power consumption reduction is required.
  • the switching means is controlled so that serial conversion is performed using a smaller number of conversion means than when high-speed reading is required or when power consumption reduction is not required.
  • the digital conversion means for converting the charge signal serially converted by the conversion means into a digital signal value, and a processing capacity that is n (n: the number of the plurality of conversion means) times, is converted by the digital conversion means.
  • Processing means for performing predetermined signal processing on the digital signal value that has been processed, and the control means is not required for a predetermined shooting that requires high-speed reading or power consumption reduction.
  • the digital signal value is processed with a processing capability of n times, and is used in the case of a predetermined photographing that does not require high-speed reading or a condition that requires a reduction in power consumption.
  • the processing means may be further controlled so as to process the digital signal value with a processing capacity reduced from n times according to the number of the conversion means.
  • control means switches to serial conversion using a single conversion means in the case of a predetermined shooting that does not require high-speed reading or a predetermined condition that requires a reduction in power consumption.
  • the means may be controlled.
  • control means performs serial conversion using a plurality of conversion means in the case of a predetermined shooting that requires high-speed reading, and the conversion used in the case of a predetermined shooting that does not require high-speed reading.
  • the switching means may be controlled to perform serial conversion using the conversion means.
  • control means includes a plurality of conversion means when performing serial conversion using a plurality of conversion means in the case of a predetermined photographing that requires high-speed reading or a predetermined condition that does not require a reduction in power consumption. Further control may be performed so that the phase of the operation cycle between the conversion means is different. By making the phases different in this way, conversion means other than the conversion means being processed can be prepared (precharge), and the transient response waiting time by the conversion means can be shortened.
  • control means may be further controlled so as to reduce the power consumption of the conversion means not in use or stop the power supply.
  • the radiographic imaging control device of the present invention includes an amplifying unit that amplifies an electric signal due to the electric charge read by the switching element at a predetermined amplification factor, and a serially converted electric charge provided corresponding to the converting unit.
  • a digital conversion means for converting the signal into a digital signal value may be mounted on an IC chip in which the amplification means, the holding means, the switching means, and the digital conversion means are integrated.
  • the present invention may be a radiographic imaging system including the radiographic imaging control device and radiation irradiating means for irradiating the radiation detector via a subject.
  • the method for controlling a radiographic image capturing apparatus includes a plurality of pixels configured to include a sensor unit that generates charges according to irradiated radiation and a switching element for reading out the charges generated by the sensor units.
  • One charge signal is inputted from each of the plurality of charge signals by inputting each charge signal held in a plurality of holding means for holding the charge signal generated by each sensor unit and read out by the switching element in the radiation detector.
  • a conversion step for performing serial conversion by a plurality of conversion means for performing serial conversion by selecting and outputting a signal, and a case or consumption of a predetermined shooting that requires high-speed reading when performing serial conversion in the conversion step In the case of predetermined conditions that do not require power reduction, serial conversion is performed using a plurality of the conversion means.
  • the switching means for switching the number of the conversion means to be used is controlled, and when performing a serial conversion in the conversion step, a high-speed reading is not required or a predetermined shooting condition or a condition where a reduction in power consumption is required. In this case, the switching means is used to serially convert the number of the conversion means to be used by using a smaller number of the conversion means than when the high-speed reading is required or when the power consumption reduction is not required. And a control step for controlling.
  • the conversion step includes a sensor unit that generates charges according to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit.
  • a plurality of inputs are made by inputting respective charge signals held in a plurality of holding means for holding a charge signal generated by each sensor unit and read out by a switching element in a radiation detector in which a plurality of pixels are arranged.
  • Serial conversion is performed by a plurality of conversion means for serial conversion by switching to one output. That is, the charge signals held in the plurality of holding means are converted into a serial charge signal by being serially converted by the plurality of conversion means.
  • the conversion means for example, a multiplexer that selects and outputs one signal from a plurality of input signals is applied.
  • a plurality of the conversion means are provided in the case of a predetermined photographing that requires high-speed reading when performing serial conversion in the conversion step or a predetermined condition that does not require power consumption reduction.
  • Controls switching means that switches the number of conversion means to be used so that serial conversion is used, and high-speed reading is not required when serial conversion is performed in the conversion step. In the case of the above condition, the number of conversion means to be used is switched so that serial conversion is performed using a smaller number of conversion means than when high-speed reading is required or power consumption reduction is not required. Control means.
  • a processing step of performing the signal processing by a processing unit that performs predetermined signal processing on the digital signal value converted by the digital conversion unit, and the control step requires high-speed reading.
  • the processing power reduced from n times according to the number of the conversion means to be used To process the digital signal values may be further control the processing means.
  • control step switching is performed so that serial conversion is performed using a single conversion means in the case of a predetermined shooting that does not require high-speed reading or in the case of a predetermined condition that requires a reduction in power consumption.
  • the means may be controlled.
  • conversion is performed using a plurality of conversion means, and the conversion used in the case of a predetermined shooting that does not require high-speed reading.
  • the switching means may be controlled to perform serial conversion using the conversion means.
  • control step when performing serial conversion using a plurality of conversion means in the case of a predetermined shooting that requires high-speed reading or a predetermined condition that does not require power consumption reduction, Further control may be performed so that the phase of the operation cycle between the conversion means is different. By making the phases different in this way, preparation can be performed (precharge) by a conversion means other than the conversion means being processed, and the transient response waiting time by the conversion means can be shortened.
  • control step it may be further controlled to reduce the power consumption of the conversion means that is not used or to stop the power supply.
  • a plurality of pixels configured to include 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 are arranged.
  • Each charge signal held in a plurality of holding means for holding a charge signal generated by each sensor unit in the radiation detector and read out by the switching element is inputted to obtain one charge signal from the plurality of charge signals.
  • a conversion step for performing serial conversion by a plurality of conversion means that perform serial conversion by selecting and outputting, and a case of predetermined photographing that requires high-speed reading when performing serial conversion in the conversion step, or power consumption reduction In the case of a predetermined condition that is not required, serial conversion is performed using a plurality of the conversion means.
  • the switching means for switching the number of the conversion means to be used is controlled, and when performing a serial conversion in the conversion step, a high-speed reading is not required or a predetermined shooting condition or a condition where a reduction in power consumption is required.
  • the switching means is used to serially convert the number of the conversion means to be used by using a smaller number of the conversion means than when the high-speed reading is required or when the power consumption reduction is not required. And causing the computer to execute a process including a control step for controlling.
  • the conversion step is configured to include 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.
  • Each charge signal held by a plurality of holding means for holding a charge signal generated by each sensor unit in a radiation detector in which a plurality of pixels are arranged and read by a switching element is inputted, and a plurality of inputs are outputted as one output.
  • the serial conversion is performed by a plurality of conversion means for serial conversion by switching to. That is, the charge signals held in the plurality of holding means are converted into a serial charge signal by being serially converted by the plurality of conversion means.
  • the conversion means for example, a multiplexer that selects and outputs one signal from a plurality of input signals is applied.
  • a plurality of the conversion means are provided in the case of a predetermined photographing that requires high-speed reading when performing serial conversion in the conversion step or a predetermined condition that does not require power consumption reduction.
  • Controls switching means that switches the number of conversion means to be used so that serial conversion is used, and high-speed reading is not required when serial conversion is performed in the conversion step. In the case of the above condition, the number of conversion means to be used is switched so that serial conversion is performed using a smaller number of conversion means than when high-speed reading is required or power consumption reduction is not required. Control means.
  • a processing step of performing the signal processing by a processing unit that performs predetermined signal processing on the digital signal value converted by the digital conversion unit, and the control step requires high-speed reading.
  • the processing power reduced from n times according to the number of the conversion means to be used To process the digital signal values may be further control the processing means.
  • control step switching is performed so that serial conversion is performed using a single conversion means in the case of a predetermined shooting that does not require high-speed reading or in the case of a predetermined condition that requires a reduction in power consumption.
  • the means may be controlled.
  • conversion is performed using a plurality of conversion means, and the conversion used in the case of a predetermined shooting that does not require high-speed reading.
  • the switching means may be controlled to perform serial conversion using the conversion means.
  • control step when performing serial conversion using a plurality of conversion means in the case of a predetermined shooting that requires high-speed reading or a predetermined condition that does not require power consumption reduction, Further control may be performed so that the phase of the operation cycle between the conversion means is different. By making the phases different in this way, preparation can be performed (precharge) by a conversion means other than the conversion means being processed, and the transient response waiting time by the conversion means can be shortened.
  • control step it may be further controlled to reduce the power consumption of the conversion means that is not used or to stop the power supply.
  • FIG. 1 is a schematic configuration diagram of a radiation information system (hereinafter referred to as “RIS” (Radiology Information System)) 10 according to the present embodiment.
  • the RIS 10 can shoot moving images in addition to still images.
  • the definition of a moving image means that still images are displayed one after another at a high speed and recognized as a moving image.
  • the still image is shot, converted into an electric signal, transmitted, and the still image is reproduced from the electric signal. This process is repeated at high speed. Therefore, the 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 depending on the degree of the “high speed” is also included in the moving image.
  • frame advance in which the same area (part or all) is photographed a plurality of times within a predetermined time and continuously reproduced depending on the degree of the “high speed” is also included in the moving image.
  • the RIS 10 is a system for managing information such as medical appointments and diagnosis records in the radiology department, and constitutes a part of a hospital information system (hereinafter referred to as “HIS” (Hospital Information System)).
  • HIS Hospital Information System
  • the RIS 10 includes a plurality of radiographic imaging systems installed individually in a plurality of imaging request terminal devices (hereinafter referred to as “terminal devices”) 12, a RIS server 14, and a radiographic room (or operating room) in a hospital.
  • terminal devices hereinafter referred to as “terminal devices”
  • RIS server a radiographic room (or operating room) in a hospital.
  • imaging system which are connected to an in-hospital network 18 composed of a wired or wireless LAN (Local Area Network) or the like.
  • the hospital network 18 is connected to an HIS server (not shown) that manages the entire HIS.
  • the imaging system 16 may be single or three or more facilities. In FIG. 1, the imaging system 16 is installed for each imaging room, but two or more imaging systems 16 are arranged in a single imaging room. May be.
  • the terminal device 12 is used by doctors and radiographers to input and view diagnostic information and facility reservations, and radiographic image capturing requests and imaging reservations are performed via the terminal device 12.
  • Each terminal device 12 includes a personal computer having a display device, and is capable of mutual communication via the RIS server 14 and the hospital network 18.
  • the RIS server 14 receives an imaging request from each terminal device 12 and manages a radiographic imaging schedule in the imaging system 16, and includes a database 14A.
  • the database 14A was photographed in the past as attribute information (name, gender, date of birth, age, blood type, weight, patient ID (Identification), etc.), medical history, medical history of the patient as the subject.
  • Information related to the patient such as a radiographic image, information related to the electronic cassette 20 used in the imaging system 16, such as an identification number (ID information), model, size, sensitivity, start date of use, number of times of use, etc.
  • ID information an identification number
  • model e.g., model, size, sensitivity, start date of use, number of times of use, etc.
  • an environment in which a radiographic image is taken using the electronic cassette 20 that is, an environment in which the electronic cassette 20 is used (for example, a radiographic room or an operating room).
  • medical-related data managed by medical institutions is stored almost permanently, and when necessary, a system (sometimes referred to as a “medical cloud”) that instantly retrieves data from the required location can be used outside the hospital. You may make it acquire the past personal information etc. of a patient (subject) from a server.
  • a system sometimes referred to as a “medical cloud”
  • the imaging system 16 captures a radiographic image by an operation of a doctor or a radiographer according to an instruction from the RIS server 14.
  • the imaging system 16 is a radiation generator that irradiates a subject with radiation X having a dose according to irradiation conditions from a radiation irradiation source 22A that emits radiation X under the control of a radiation irradiation control unit 22 (see FIG. 4). 24 and a radiation detector 26 (see FIG. 3) that generates radiation by absorbing the radiation X that has passed through the region to be imaged of the subject and generates image information indicating a radiation image based on the amount of the generated charge.
  • a built-in electronic cassette 20, a cradle 28 for charging a battery built in the electronic cassette 20, and a console 30 for controlling the electronic cassette 20 and the radiation generator 24 are provided.
  • the console 30 acquires various types of information included in the database 14A from the RIS server 14 and stores them in an HDD 88 (see FIG. 4), which will be described later, and uses the information as necessary to use the electronic cassette 20 and the radiation generator 24. Control.
  • FIG. 2 shows an example of the arrangement state of each device in the radiation imaging room 32 of the imaging system 16 according to the present embodiment.
  • the radiation imaging room 32 there are a standing table 34 used when performing radiography in a standing position and a prone table 36 used when performing radiation imaging in a lying position. It is installed.
  • the space in front of the standing table 34 is the imaging position of the subject 38 when performing radiography in the standing position, and the space above the supine table 36 is the subject 40 in performing radiography in the prone position. This is the shooting position.
  • the standing table 34 is provided with a holding unit 42 that holds the electronic cassette 20, and the electronic cassette 20 is held by the holding unit 42 when a radiographic image is taken in the standing position.
  • a holding unit 44 that holds the electronic cassette 20 is provided in the lying position table 36, and the electronic cassette 20 is held by the holding unit 44 when a radiographic image is taken in the lying position.
  • the radiation irradiation source 22A is arranged around a horizontal axis in order to enable radiation imaging in a standing position and in a supine position by radiation from a single radiation irradiation source 22A.
  • a support movement mechanism 46 that can be rotated in the direction of arrow A in FIG. 2, can move in the vertical direction (in the direction of arrow B in FIG. 2), and can move in the horizontal direction (in the direction of arrow C in FIG. 2). Is provided.
  • the drive source that moves (including rotation) in the directions of arrows A to C in FIG. 2 is built in the support moving mechanism 46, and is not shown here.
  • the cradle 28 is formed with an accommodating portion 28A capable of accommodating the electronic cassette 20.
  • the built-in battery is charged in a state of being accommodated in the accommodating portion 28A of the cradle 28.
  • the electronic cassette 20 is taken out of the cradle 28 by a radiographer or the like, and the photographing posture is established. If it is in the upright position, it is held in the holding part 42 of the standing table 34, and if it is in the upright position, it is held in the holding part 44 of the standing table 36.
  • various types of information are transmitted and received by radio communication between the radiation generator 24 and the console 30 and between the electronic cassette 20 and the console 30 (details will be described later). .
  • the electronic cassette 20 is not used only in the state of being held by the holding portion 42 of the standing base 34 or the holding portion 44 of the prone position base 36. When photographing, it can be used in a state where it is not held by the holding unit.
  • the electronic cassette 20 incorporates a radiation detector described later.
  • the built-in radiation detector is an indirect conversion method that converts radiation into light with a scintillator and then converts it into charges with a photoelectric conversion element such as a photodiode, and a direct conversion method that converts radiation into charges with a semiconductor layer such as amorphous selenium. Either may be used.
  • the direct conversion type radiation detector is configured by laminating a photoelectric conversion layer that absorbs radiation X and converts it into charges on a TFT active matrix substrate.
  • the photoelectric conversion layer is made of amorphous a-Se (amorphous selenium) containing, for example, selenium as a main component (for example, a content rate of 50% or more), and when irradiated with radiation X, a charge corresponding to the amount of irradiated radiation. By generating a certain amount of charge (electron-hole pairs) internally, the irradiated radiation X is converted into a charge.
  • An indirect conversion type radiation detector indirectly uses a phosphor material and a photoelectric conversion element (photodiode) instead of the radiation-to-charge conversion material that directly converts the radiation X such as amorphous selenium into an electric charge. It may be converted into an electric charge.
  • GOS gadolinium oxysulfide
  • CsI cesium iodide
  • FIG. 3A is a schematic cross-sectional view schematically showing the configuration of the four pixel portions of the radiation detector 26 provided in the electronic cassette 20, and FIG. 3B is a diagram showing the electrical configuration of the pixel portion of the radiation detector 26. It is.
  • a signal output unit 52, a sensor unit 54 (TFT substrate 74), and a scintillator 56 are sequentially laminated on an insulating substrate 50, and the signal output unit 52,
  • the sensor unit 54 constitutes a pixel group of the TFT substrate 74. That is, the plurality of pixels are arranged in a matrix on the substrate 50, and the signal output unit 52 and the sensor unit 54 in each pixel are configured to overlap each other.
  • An insulating film 53 is interposed between the signal output unit 52 and the sensor unit 54.
  • the scintillator 56 is formed on the sensor unit 54 via a transparent insulating film 58, and forms a phosphor that emits light by converting radiation incident from above (opposite side of the substrate 50) or below into light. It is what. Providing such a scintillator 56 absorbs radiation transmitted through the subject and emits light.
  • the wavelength range of light emitted by the scintillator 56 is preferably in the visible light range (wavelength 360 nm to 830 nm), and in order to enable monochrome imaging by the radiation detector 26, the wavelength range of green is included. Is more preferable.
  • the phosphor used in the scintillator 56 preferably contains cesium iodide (CsI) when imaging using X-rays as radiation, and has an emission spectrum of 400 nm to 700 nm upon X-ray irradiation. It is particularly preferable to use CsI (Tl) (cesium iodide with thallium added). Note that the emission peak wavelength of CsI (Tl) in the visible light region is 565 nm.
  • CsI cesium iodide
  • ISS Irradiation Side Sampling
  • PSS Penetration Side Sampling
  • the light emission position of the scintillator is closer to each other, so that the resolution of the radiographic image obtained by imaging is higher, and the amount of light received by the TFT substrate is increased, and as a result, the sensitivity of the radiographic image is improved.
  • the sensor unit 54 includes an upper electrode 60, a lower electrode 62, and a photoelectric conversion film 64 disposed between the upper and lower electrodes.
  • the photoelectric conversion film 64 is made of an organic photoelectric conversion material that generates charges by absorbing light emitted from the scintillator 56.
  • the upper electrode 60 Since it is necessary for the upper electrode 60 to cause the light generated by the scintillator 56 to enter the photoelectric conversion film 64, it is preferable that the upper electrode 60 be made of a conductive material that is transparent at least with respect to the emission wavelength of the scintillator 56. 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 60, the TCO is preferable because it tends to increase the resistance when it is desired to obtain a transmittance of 90% or more.
  • TCO transparent conductive oxide
  • the upper electrode 60 may have a single configuration common to all pixels, or may be divided for each pixel.
  • the photoelectric conversion film 64 includes an organic photoelectric conversion material, absorbs light emitted from the scintillator 56, and generates electric charge according to the absorbed light.
  • the photoelectric conversion film 64 including the organic photoelectric conversion material has a sharp absorption spectrum in the visible region, and electromagnetic waves other than light emitted by the scintillator 56 are hardly absorbed by the photoelectric conversion film 64, and X-rays are obtained.
  • the noise generated by the radiation such as being absorbed by the photoelectric conversion film 64 can be effectively suppressed.
  • the organic photoelectric conversion material constituting the photoelectric conversion film 64 is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the scintillator 56 in order to absorb light emitted by the scintillator 56 most efficiently.
  • the absorption peak wavelength of the organic photoelectric conversion material matches the emission peak wavelength of the scintillator 56, but if the difference between the two is small, the light emitted from the scintillator 56 can be sufficiently absorbed.
  • the difference between the absorption peak wavelength of the organic photoelectric conversion material and the emission peak wavelength with respect to the radiation of the scintillator 56 is preferably within 10 nm, and more preferably within 5 nm.
  • the organic photoelectric conversion material examples include quinacridone organic compounds and phthalocyanine organic compounds.
  • quinacridone 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 56, the difference in peak wavelength can be made within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 64 can be substantially maximized.
  • the photoelectric conversion film 64 including an organic photoelectric conversion material is described as an example. However, the present invention is not limited thereto, and the photoelectric conversion film 64 may be a material that absorbs light and generates charges. For example, other materials such as amorphous silicon may be applied. When the photoelectric conversion film 64 is composed of amorphous silicon, it can be configured to absorb light emitted from the scintillator over a wide wavelength range.
  • the sensor unit 54 constituting each pixel only needs to include at least the lower electrode 62, the photoelectric conversion film 64, and the upper electrode 60.
  • the electron blocking film 66 and the hole blocking film are used. It is preferable to provide at least one of 68, and it is more preferable to provide both.
  • the electron blocking film 66 can be provided between the lower electrode 62 and the photoelectric conversion film 64.
  • a bias voltage is applied between the lower electrode 62 and the upper electrode 60, electrons are transferred from the lower electrode 62 to the photoelectric conversion film 64. It is possible to suppress the dark current from increasing due to the injection of.
  • An electron donating organic material can be used for the electron blocking film 66.
  • the hole blocking film 68 can be provided between the photoelectric conversion film 64 and the upper electrode 60. When a bias voltage is applied between the lower electrode 62 and the upper electrode 60, the hole blocking film 68 is transferred from the upper electrode 60 to the photoelectric conversion film 64. It is possible to suppress the increase in dark current due to the injection of holes.
  • An electron-accepting organic material can be used for the hole blocking film 68.
  • the signal output unit 52 corresponds to the lower electrode 62, a capacitor 70 that accumulates the electric charge transferred to the lower electrode 62, and a field effect thin film transistor (Thin) that converts the electric charge accumulated in the capacitor 70 into an electric signal and outputs it.
  • Film-Transistor (hereinafter sometimes simply referred to as a thin film transistor) 72 is formed.
  • the region in which the capacitor 70 and the thin film transistor 72 are formed has a portion that overlaps the lower electrode 62 in plan view. With this configuration, the signal output unit 52 and the sensor unit 54 in each pixel are thick. There will be overlap in the vertical direction. In order to minimize the plane area of the radiation detector 26 (pixel), it is desirable that the region where the capacitor 70 and the thin film transistor 72 are formed is completely covered with the lower electrode 62.
  • the signal output units 52 in the pixels arranged in a matrix are extended in a certain direction (the scanning line direction in FIG. 3B, hereinafter also referred to as “row direction”), and the thin film transistors 72 of the individual pixels.
  • a plurality of gate wirings G for turning on and off, and extending in a direction intersecting with the gate wiring G (signal wiring direction in FIG. 3B, hereinafter also referred to as “column direction”), and turned on through the thin film transistor 72 that is turned on.
  • a plurality of data wirings D for reading out the accumulated charges from the capacitor 70 are provided.
  • Individual gate lines G are connected to a gate line driver 71, and individual data lines D are connected to a signal processing unit 73.
  • the thin film transistors 72 of the individual pixel units are sequentially turned on in units of rows by a signal supplied from the gate line driver 71 via the gate wiring G.
  • the electric charge accumulated in the capacitor 70 of the pixel portion in which the thin film transistor 72 is turned on is transmitted through the data wiring D as an analog electric signal and input to the signal processing unit 73. Therefore, the electric charges accumulated in the capacitors 70 of the individual pixel portions are sequentially read out in units of rows.
  • the gate line driver 71 sequentially outputs an on signal to each gate line G one line at a time in one image reading operation, and reads out the electric charge accumulated in the capacitor 70 of each pixel unit line by line.
  • an ON signal is sequentially output from the gate line driver 71 to each gate wiring G by a plurality of lines (for example, two lines or four lines) in a single image reading operation. It is possible to read out the charge accumulated in the capacitor 70 of each pixel unit (by combining and reading out the charges of the pixels read out simultaneously) by the binning readout method, and the image is sequentially transferred to the readout method and the binning readout method.
  • the reading method can be switched.
  • the sequential scanning method and the gate wiring G are divided into odd and even rows for each row, and an ON signal is output to the odd or even gate wiring G for each image reading operation.
  • the image reading method may be switched between an interlaced scanning method (so-called interlaced scanning method) that reads out charges accumulated in each pixel portion alternately for each line.
  • the signal processing unit 73 and the gate line driver 71 are connected to a cassette control unit 69, and the gate control unit 69 controls the gate line driver 71 and the signal processing unit 73.
  • the cassette control unit 69 is composed of a microcomputer including a CPU, ROM, RAM, HDD, fresh memory, and the like.
  • each pixel in the radiation detector 26 is not limited to the matrix arrangement arranged in rows and columns, and other arrangements such as a staggered arrangement may be applied.
  • the pixel shape may be a rectangular pixel shape or a polygonal shape such as a honeycomb shape.
  • FIG. 4 is a block diagram illustrating a schematic configuration of a signal processing unit of the radiation detector 26 according to the present embodiment
  • FIG. 5 is an equivalent view focusing on one pixel portion of the radiation detector 26 according to the present embodiment. It is a figure which shows a circuit.
  • the electric charge photoelectrically converted by the scintillator 56 is read and output to the signal processing unit 73 when the thin film transistor 72 is turned on.
  • the signal processing unit 73 includes a charge amplifier 75 as an amplification unit, a sample hold circuit 76 as a holding unit, a multiplexer 77 as a conversion unit, and an A / D converter 78 as a digital conversion unit. I have.
  • the electric charge read out by the thin film transistor 72 is integrated by the charge amplifier 75, amplified by a predetermined amplification factor, held by the sample hold circuit, and output to the A / D converter 78 via the multiplexer 77. .
  • the analog signal is converted into a digital signal value by the A / D converter 78 so that image processing can be performed.
  • the source of the thin film transistor 72 is connected to the data line D, and the data line D is connected to the charge amplifier 75.
  • the drain of the thin film transistor 72 is connected to the capacitor 70, and the gate of the thin film transistor 72 is connected to the gate wiring G.
  • the charge amplifier 75 may be provided corresponding to each pixel (thin film transistor 72), may be provided for each column (data wiring D), or may be provided in a predetermined group (for example, 3). X3 pixels or the like) or may be provided for each predetermined column group (for example, a plurality of data lines D).
  • the charge signals transmitted through the individual data lines D are integrated by the charge amplifier 75 and held in the sample and hold circuit 76.
  • the charge amplifier 75 is provided with a reset switch 79. While the reset switch 79 is turned off, the charge is read out and the charge signal is held in the sample hold circuit 76. When the reading of the charge is completed, the reset switch 79 is turned on to release the charge remaining in the integrating capacitor C1 of the charge amplifier 75 and reset it.
  • the charge signal held in the sample hold circuit 76 is converted into an analog voltage, input to the multiplexer 77, serially converted, and converted into digital image information by the A / D converter 78.
  • the cassette control unit 69 controls on / off of the thin film transistor 72 and on / off of the reset switch 79 of the charge amplifier 75.
  • FIG. 6 is a control block diagram of the imaging system 16 according to the present embodiment.
  • the console 30 is configured as a server computer, and includes a display 80 that displays an operation menu, a captured radiographic image, and the like, and a plurality of keys, and an operation panel on which various information and operation instructions are input. 82.
  • the console 30 includes a CPU 84 that controls the operation of the entire apparatus, a ROM 86 that stores various programs including a control program in advance, a RAM 87 that temporarily stores various data, and various data.
  • An HDD (Hard Disk Drive) 88 that stores and holds, a display driver 92 that controls display of various types of information on the display 80, and an operation input detector 90 that detects an operation state of the operation panel 82 are provided. .
  • the console 30 transmits and receives various information such as irradiation conditions to be described later between the image processing device 23 and the radiation generation device 24 by wireless communication, and also various information such as image data with the electronic cassette 20.
  • various information such as irradiation conditions to be described later between the image processing device 23 and the radiation generation device 24 by wireless communication, and also various information such as image data with the electronic cassette 20.
  • I / F for example, a wireless communication unit
  • I / O 94 are provided with an I / O 94.
  • the CPU 84, ROM 86, RAM 87, HDD 88, display driver 92, operation input detection unit 90, I / O 94, and wireless communication unit 96 are connected to each other via a bus 98 such as a system bus or a control bus. Therefore, the CPU 84 can access the ROM 86, RAM 87, and HDD 88, controls display of various information on the display 80 via the display driver 92, and the radiation generator 24 via the wireless communication unit 96. Control of transmission and reception of various types of information with the electronic cassette 20 can be performed. Further, the CPU 84 can grasp the operation state of the user with respect to the operation panel 82 via the operation input detection unit 90.
  • the image processing device 23 includes an I / F (for example, a wireless communication unit) 100 that transmits and receives various types of information such as irradiation conditions to and from the console 30, and the electronic cassette 20 and the radiation generation device 24 based on the irradiation conditions. And an image processing control unit 102 for controlling. Further, the radiation generator 24 includes a radiation irradiation control unit 22 that controls radiation irradiation from the radiation irradiation source 22A.
  • I / F for example, a wireless communication unit
  • the radiation generator 24 includes a radiation irradiation control unit 22 that controls radiation irradiation from the radiation irradiation source 22A.
  • the image processing control unit 102 includes a system control unit 104, a panel control unit 106, and an image processing control unit 108, and exchanges information with each other via a bus 110.
  • the panel control unit 106 receives information from the electronic cassette 20 wirelessly or by wire, and the image processing control unit 108 performs image processing.
  • the system control unit 104 receives information such as tube voltage and tube current as irradiation conditions from the console 30, and irradiates radiation X from the radiation irradiation source 22A of the radiation irradiation control unit 22 based on the received irradiation conditions. Take control.
  • the charge signals held in the sample and hold circuit 76 are input to the multiplexer 77, and one charge signal is selected from a plurality of charge signals and output in order. (Serial) is output, and the analog electric signal is converted into a digital electric signal by the A / D converter 78.
  • the switching speed is limited, and the reading speed is improved. It is an obstacle.
  • FIG. 7 is a block diagram for explaining a portion related to the multiplexer 77 of the present invention.
  • two multiplexers 77 are provided as the plurality of multiplexers 77.
  • One multiplexer A77A is connected to sample hold circuits 76A, 76B, 76C, and 76D that hold the outputs of 1ch to 4ch charge amplifiers 75A, 75B, 75C, and 75D, respectively. Further, a switch 81 as a switching means is provided between the even-numbered sample hold circuit 76 (76B, 76D) and the multiplexer A77A, and the even-channel sample-hold circuit 76 (76B, 76B, 76B) is provided via the switch 81. 76D) and the multiplexer B77B are connected.
  • the switch 81 is controlled by the cassette control unit 69, and the output destination of the charge signal held by the even-ch sample hold circuit 76 (76B, 76D) is switched to the multiplexer A77A or the multiplexer B77B. That is, the switch 81 switches between the case where only the multiplexer A77A is used and the case where both the multiplexer A77A and the multiplexer B77B are used.
  • an A / D converter A78A is connected to the multiplexer A77A
  • an A / D converter B78B is connected to the multiplexer B77B.
  • the respective charge signals serially converted by the multiplexer A77A and the multiplexer B77B are converted into digital image information by the respective A / D converters 78 (78A, 78B), and output to the cassette control unit 69.
  • various signal processing is performed on the digital signal value.
  • the multiplexer A77A and the A / D converter A78A are used, and the multiplexer B77B and the A / D converter B78B consumes power in the sleep or power down mode. It is controlled by the cassette control unit 69 so as to suppress this.
  • the cassette control unit is configured to use the multiplexer B77B and the A / D converter B78B in addition to the multiplexer A77A and the A / D converter A78A.
  • 69 controls the switch 81 to reduce the number of channels (read lines) to be switched by one multiplexer 77 (half in the present embodiment), thereby improving the read speed by a factor of two.
  • the reading speed is improved by a factor of two (several times the multiplexer), so that the cassette control unit is converted after being converted by the A / D converter.
  • the processing capacity of the digital processing performed in 69 is twice that of the multiplexer (several times of the multiplexer).
  • the processing capacity of the digital processing performed by the cassette control unit 69 becomes redundant. Therefore, the operation clock of the cassette control unit 69 is clocked according to the number of multiplexers 77 to be used. Digital processing is performed by lowering the processing capacity. Thereby, the power consumption can be further reduced.
  • the multiplexer A77A is responsible for odd-numbered channels and the multiplexer B77B is responsible for even-numbered channels.
  • the present invention is not limited to this.
  • FIG. ch may be assigned.
  • FIG. 8 shows an example in which a switch 81 is provided between the 3ch and 4ch sample hold circuits 76 (76C, 76D) and the multiplexer A77A for switching.
  • the signal processing unit 73 including the charge amplifier 75, the sample hold circuit 76, the multiplexer 77, and the A / D converter 78 is a one-chip IC. Since the A / D converter 78 is reduced by miniaturization and becomes significantly smaller than an analog circuit unit such as the charge amplifier 75 that is unlikely to benefit from miniaturization such as RC, the merit of integration is great.
  • FIG. 9 is a flowchart showing the radiographic imaging preparation control routine.
  • step 200 it is determined whether or not a shooting instruction has been issued. If the determination is negative, the routine ends. If the determination is affirmative, the routine proceeds to step 202.
  • step 202 an initial information input screen is displayed on the display 80, and the process proceeds to step 204. That is, the display driver 92 is controlled to display a predetermined initial information input screen on the display 80.
  • step 204 it is determined whether or not predetermined information has been input.
  • the process waits until the determination is affirmed, and the process proceeds to step 206.
  • the initial information input screen for example, the name of the subject who is going to take a radiographic image, the part to be imaged, the posture at the time of imaging, and the irradiation condition of the radiation X at the time of imaging (in this embodiment, the radiation X is irradiated)
  • Message for prompting the input of the tube voltage and tube current) and an input area for such information are displayed.
  • the photographer When the initial information input screen is displayed on the display 80, the photographer displays the name of the subject to be imaged, the region to be imaged, the posture at the time of imaging, and the irradiation conditions in the corresponding input areas on the operation panel 82. Enter through.
  • the radiographer enters the radiography room 32 together with the subject.
  • the radio cassette 22A is supported while holding the electronic cassette 20 in the holding unit 44 of the corresponding prone position table 36.
  • the subject is positioned (positioned) at a predetermined imaging position.
  • the subject and the electronic cassette 20 are ready to capture the imaging target site.
  • the radiation source 22A are positioned (positioned).
  • step 204 is affirmed and the routine proceeds to step 206.
  • step 204 is an infinite loop, but it may be forcibly terminated by operating a cancel button provided on the operation panel 82.
  • step 206 information input on the initial information input screen (hereinafter referred to as “initial information”) is transmitted to the electronic cassette 20 via the wireless communication unit 96, and then the process proceeds to the next step 208.
  • the irradiation conditions included in the initial information are set by transmitting the irradiation conditions to the radiation generator 24 via the wireless communication unit 96.
  • the image processing control unit 102 of the radiation generator 24 prepares for irradiation under the received irradiation conditions.
  • step 210 the start of ABC control is instructed, and then the process proceeds to step 212, where the instruction information instructing the start of radiation irradiation is transmitted to the radiation generator 24 via the wireless communication unit 96. Ends.
  • FIG. 10 is a flowchart showing a radiation irradiation control routine.
  • step 300 it is determined whether or not there has been an irradiation start instruction. If a negative determination is made, this routine ends. If an affirmative determination is made, the routine proceeds to step 302.
  • step 302 the steady-state radiation dose (initial value) XN is read, and the process proceeds to step 304.
  • step 304 irradiation is started with the read steady-state radiation dose, and the process proceeds to step 306. That is, irradiation from the radiation irradiation source 22 ⁇ / b> A is started by applying a tube voltage and a tube current corresponding to the irradiation upper limit received from the console 30 to the radiation generator 24. The radiation X emitted from the radiation source 22A passes through the subject and reaches the electronic cassette 20.
  • step 306 currently stored radiation dose correction information is read, and the process proceeds to step 306.
  • This radiation dose correction information is generated by ABC control and is stored as a correction coefficient ⁇ X.
  • step 308 correction processing based on ABC control is executed, and the process proceeds to step 310. That is, based on the gradation signal (QL value) obtained from the electronic cassette 20, an average value of the QL values of the region of interest image is calculated, and the average value of the QL values is compared with a predetermined threshold value. The radiation dose is feedback controlled so as to converge to the threshold value.
  • QL value the gradation signal
  • step 310 it is determined whether or not an instruction to end shooting is given. If the determination is affirmative, the process proceeds to step 312. If the determination is negative, the process returns to step 306 and the above-described processing is repeated.
  • step 312 the irradiation is terminated, and the radiographic image capturing control is terminated.
  • FIG. 11 is a flowchart showing an image processing control routine.
  • step 400 gradation information for one frame is sequentially captured, and the process proceeds to step 402. That is, the gradation signal generated by the TFT substrate 74 of the electronic cassette 20 is sequentially taken into the image processing control unit 102 under the control of the panel control unit 106. Before the gradation signal is captured by the image processing control unit 102, the gradation signal is sequentially captured in the cassette control unit 69 by a gradation signal capturing process described later, and the gradation signal captured by the cassette control unit 69 is sequentially displayed on the panel. The image is sent to the image processing control unit 102 under the control of the control unit 106.
  • step 402 a still image is generated, and the process proceeds to step 403. That is, a still image is generated when a grayscale signal for one frame is captured.
  • step 403 it is determined whether or not moving image shooting is performed. If the determination is affirmative, the process proceeds to step 404. If the determination is negative, the image processing control is terminated as it is.
  • step 404 the moving image editing process is performed, and the process proceeds to step 406.
  • moving image editing is performed by combining still images for each frame generated in step 402.
  • step 406 image display processing is performed, and the process proceeds to step 408.
  • the moving image generated by the moving image editing process is sent to the display driver 92, whereby the display driver 92 displays the moving image.
  • step 408 the region of interest is set, and the process proceeds to step 409.
  • the region of interest is set by, for example, pattern matching or detecting a region with a large amount of movement, but the region of interest may be set by a user operation.
  • step 410 the gradation signal of the set region of interest is extracted, and the process proceeds to step 412.
  • step 412 the average QL value of the gradation signal of the region of interest is calculated and the process proceeds to step 414, the pre-stored reference QL value is read, and the process proceeds to step 416.
  • step 416 the calculated average QL value is compared with the read reference QL value to determine whether correction is possible or not, and the process proceeds to step 418.
  • the determination as to whether or not correction is possible may be a so-called on / off determination in which a predetermined amount of correction is performed if the difference is greater than or equal to a predetermined value and no correction is performed if the difference is less than a predetermined value. Then, based on the difference, it may be a solution of a calculation by a predetermined calculation formula (for example, a calculation formula based on PID control or the like).
  • step 418 radiation dose correction information ⁇ X is generated based on the comparison / correction determination result in step 416, and the process proceeds to step 420.
  • step 420 the generated correction information ⁇ X is stored, and the image processing control is terminated.
  • FIG. 12 is a flowchart showing a frame capture processing routine.
  • step 500 When capturing a gradation signal, it is first determined in step 500 whether or not it is still image shooting. If the determination is affirmative, the process proceeds to step 502, and if the determination is negative, the process proceeds to step 506. .
  • step 502 the switch 81 is controlled by the cassette control unit 69 to use one multiplexer A77A, and the process proceeds to step 504.
  • the switch 81 is controlled so that all the charge signals held by the sample hold circuit 76 of 1ch to 4ch are input to the multiplexer A77A.
  • step 504 power to at least one of the unused multiplexer B77B and A / D converter B78B is turned off, and the process proceeds to step 508. That is, when reading is performed slowly without requiring high-speed reading, power consumption can be reduced by turning off the power of the multiplexer 77 and the A / D converter 78 that are not used. At this time, in the present embodiment, in the digital processing performed by the cassette control unit 69 after A / D conversion, the digital processing is performed by reducing the processing capability by clocking down to 1 ⁇ 2. Thereby, the power consumption can be further reduced.
  • the switch 81 is controlled by the cassette control unit 69 so as to use the two multiplexers 77 (77A, 77B). That is, in the example of FIG. 7, the switch 81 is controlled such that the odd-channel charge signal is processed by the multiplexer A77A and the even-channel charge signal is processed by the multiplexer B77B.
  • the on / off operation cycle of the multiplexers A77A and B77B (multiplexers A and B in FIG. 13), and the A / D converters A78A and A / D converters B78B.
  • the operation cycle (A / D converters CLK1 and CLK2 in FIG. 13) is shifted by a half cycle.
  • processing by the multiplexer A77A and processing by the multiplexer B77B, processing by the A / D converter A78A for the output of the multiplexer A78A, and processing by the A / D converter B78B for the output of the multiplexer B77B are alternately performed. Thereby, preparation and signal reception are performed in the other multiplexer 77 while one multiplexer 77 is connected (precharge processing). Therefore, the processing by the two multiplexers 77 and the A / D converter 78 can shorten the waiting time for the transient response of the multiplexer 77.
  • FIG. 13 shows an example in which the operation cycle of the multiplexer A77A and the multiplexer B77B and the operation cycle of the A / D converter A78A and the A / D converter B78B are shifted by a half cycle. It is not limited. For example, it may be shifted by 1/3 period or may be shifted by 1/4 period.
  • step 508 gradation information for one frame is sequentially read, and the process proceeds to step 510, where it is determined whether or not the photographing is finished. If the determination in step 510 is negative, the process returns to step 500 and the above-described processing is repeated. When the determination is positive, the series of processing ends.
  • a plurality of multiplexers 77 and a switch 81 for switching the number of multiplexers 77 to be used are provided, and a plurality of multiplexers 77 are used in the case of moving image shooting that needs to be read at high speed. If the switch 81 is controlled so that it is not necessary to read at high speed (for example, still image shooting), the switch 81 is controlled so that one multiplexer 77 is used. By processing with a plurality of multiplexers 77, the waiting time for the transient response of the multiplexer 77 can be shortened and the reading time can be shortened.
  • one multiplexer 77 is used and the other multiplexers 77 are turned off, so that power consumption can be reduced. Therefore, it is possible to simultaneously reduce the transient response waiting time of the multiplexer and the power consumption.
  • the switch 81 is switched so as to use a plurality of multiplexers 77 in the case of moving image shooting as a case where reading at high speed is necessary. Is not limited to moving image shooting, and when it is necessary to read still images even at high speed, the switch 81 may be switched to use a plurality of multiplexers 77.
  • still image shooting has been described as an example when it is not necessary to read at high speed, in this case as well, in the case of moving image shooting, the frame rate may be lower than a predetermined value.
  • the switch 81 may be switched to use the multiplexer 77 and the other multiplexers 77 may be turned off to reduce power consumption.
  • an example in which two multiplexers 77A and 77B are provided as the plurality of multiplexers 77 is not limited to two, and three or more multiplexers 77 may be provided.
  • the number of multiplexers 77 to be used may be changed according to the required reading speed. That is, when one multiplexer 77 is used, when two multiplexers 77 are used, the case where three multiplexers 77 are used can be switched according to the required reading speed, and high speed is required. It is sufficient to increase the number of multiplexers 77 used.
  • a plurality of multiplexers 77 are used in the case of a predetermined shooting that requires high-speed reading, and the multiplexer 77 that is used in the case of a predetermined shooting that does not require high-speed reading.
  • the condition for switching the number of multiplexers 77 to be used is not limited to the necessity of high-speed reading. Instead of necessity of high-speed reading, the number of multiplexers 77 to be used may be switched according to necessity of reduction of power consumption. Specifically, in the condition where commercial power is supplied from an outlet, since there is less concern about the power supply compared to battery driving, a plurality of multiplexers 77 are used to reduce the power consumption.
  • the power consumption can be reduced by switching to use a smaller number of multiplexers 77 than when commercial power is supplied. Further, when switching to use a smaller number of multiplexers 77 than when commercial power is supplied, the multiplexer 77 that uses the processing capability of digital processing performed by the cassette control unit 69 after A / D conversion. The power consumption can be further reduced by performing digital processing by reducing the processing capacity by clocking down according to the number.
  • processing shown in each flowchart in the above embodiment may be stored and distributed as various programs in various storage media.
  • the present invention is not limited to this, and includes other radiation such as ⁇ -rays and ⁇ -rays.

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Abstract

L'invention concerne un dispositif de commande de radiographie qui comprend : un détecteur de rayonnement ; une pluralité de moyens de conversion servant à la conversion en série en sélectionnant et en délivrant un signal de charge depuis une pluralité de signaux de charge qui sont conservés par une pluralité de moyens de conservation qui conservent les signaux de charge qui sont émis avec chaque partie de détecteur du détecteur de rayonnement et lus par des éléments de commutation ; un moyen de commutation permettant de commuter le nombre de moyens de conversion ; et un moyen de commande destiné à commander le moyen de commutation de telle manière que, dans une photographie prédéterminée dans laquelle une lecture à grande vitesse est nécessaire ou dans une condition prédéfinie dans laquelle la minimisation de la consommation d'énergie n'est pas nécessaire, une conversion en série est effectuée à l'aide de la pluralité de moyens de conversion, et dans une photographie prédéterminée dans laquelle la lecture à grande vitesse n'est pas nécessaire ou dans une condition dans laquelle la minimisation de la consommation d'énergie est nécessaire, un faible nombre de moyens de conversion est utilisé dans la conversion en série.
PCT/JP2012/080094 2012-03-16 2012-11-20 Dispositif de commande de radiographie, système de radiographie, procédé de commande du dispositif de radiographie, et programme de commande de radiographie WO2013136597A1 (fr)

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WO2019004230A1 (fr) * 2017-06-28 2019-01-03 富士フイルム株式会社 Dispositif de détection d'image radiographique et son procédé de fonctionnement
WO2019004232A1 (fr) * 2017-06-28 2019-01-03 富士フイルム株式会社 Dispositif de détection d'image de radiographie et son procédé de fonctionnement
CN110800289A (zh) * 2017-06-28 2020-02-14 富士胶片株式会社 放射线图像检测装置及其工作方法

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WO2019004230A1 (fr) * 2017-06-28 2019-01-03 富士フイルム株式会社 Dispositif de détection d'image radiographique et son procédé de fonctionnement
WO2019004232A1 (fr) * 2017-06-28 2019-01-03 富士フイルム株式会社 Dispositif de détection d'image de radiographie et son procédé de fonctionnement
CN110800288A (zh) * 2017-06-28 2020-02-14 富士胶片株式会社 放射线图像检测装置及其工作方法
CN110800289A (zh) * 2017-06-28 2020-02-14 富士胶片株式会社 放射线图像检测装置及其工作方法
CN110832848A (zh) * 2017-06-28 2020-02-21 富士胶片株式会社 放射线图像检测装置及其工作方法
JPWO2019004232A1 (ja) * 2017-06-28 2020-04-02 富士フイルム株式会社 放射線画像検出装置とその作動方法
JPWO2019004230A1 (ja) * 2017-06-28 2020-04-23 富士フイルム株式会社 放射線画像検出装置とその作動方法
US10992885B2 (en) 2017-06-28 2021-04-27 Fujifilm Corporation Radiographic image detection device and method for operating the same
US11064966B2 (en) 2017-06-28 2021-07-20 Fujifilm Corporation Radiographic image detection device and method for operating the same
CN110800289B (zh) * 2017-06-28 2021-10-29 富士胶片株式会社 放射线图像检测装置及其工作方法
CN110832848B (zh) * 2017-06-28 2021-10-29 富士胶片株式会社 放射线图像检测装置及其工作方法
CN110800288B (zh) * 2017-06-28 2021-12-21 富士胶片株式会社 放射线图像检测装置及其工作方法

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