WO2014050532A1 - Dispositif de radiographie, système de radiographie, procédé de commande de dispositif de radiographie et programme de radiographie - Google Patents

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

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Publication number
WO2014050532A1
WO2014050532A1 PCT/JP2013/074324 JP2013074324W WO2014050532A1 WO 2014050532 A1 WO2014050532 A1 WO 2014050532A1 JP 2013074324 W JP2013074324 W JP 2013074324W WO 2014050532 A1 WO2014050532 A1 WO 2014050532A1
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Prior art keywords
timing
control
detection
switching element
pixel
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PCT/JP2013/074324
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English (en)
Japanese (ja)
Inventor
北野　浩一
美広 岡田
西納　直行
中津川　晴康
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富士フイルム株式会社
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Publication of WO2014050532A1 publication Critical patent/WO2014050532A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • 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
    • 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 image capturing apparatus, a radiographic image capturing system, a control method for the radiographic image capturing apparatus, and a radiographic image capturing 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.
  • a substrate in which a pixel unit including a storage capacitor that accumulates charges generated in a photoelectric conversion layer according to irradiation radiation and a TFT that is turned on by a turn-on signal from a gate wiring is arranged in a matrix.
  • an image detection device in which a dummy pixel group including a dummy wiring intersecting with each data wiring and a TFT corresponding to each data wiring is provided, and a correction capacitor is connected to each data wiring.
  • pixels having a conversion element for converting radiation or light into electric charge and an output switch element for performing an output operation for outputting an electric signal based on the electric charge are arranged in a matrix.
  • a plurality of converters arranged in a row, an output drive circuit for controlling the output operation of the converters in units of rows, a transmission path for transmitting the output electric signal, and reading via the transmission path A read-out circuit for performing a sample-hold operation for temporarily holding the electrical signal and a reset operation for resetting the transmission path, a sample-hold operation after the start of the output operation, a reset operation after the sample-hold operation, and a post-reset operation
  • an imaging apparatus including a control unit that controls an output driving circuit and a readout circuit so that the end of the output operation is sequentially performed in units of rows.
  • the feedthrough noise does not always occur with the same magnitude and time constant, but has temperature dependence and the like.
  • the feedthrough noise is generated when a temperature change occurs. Cannot be reliably suppressed.
  • Patent Document 2 describes that feedthrough noise is accurately suppressed even when the ambient temperature changes.
  • the technique described in Patent Document 2 uses a dummy line to reduce feedthrough noise. There is room for improvement because the feedthrough noise of the dummy line and the feedthrough noise of the actual pixel do not exactly match.
  • the present invention has been made in consideration of the above-described facts, and an object thereof is to reliably suppress feedthrough noise in consideration of actual device characteristic variations and dynamic changes.
  • a radiographic imaging apparatus of the present invention includes a sensor unit that generates electric charge according to irradiated radiation, and a switching element that reads out the electric charge generated by the sensor unit and outputs it to a signal line.
  • a radiation detector in which a plurality of pixels composed of a plurality of pixels are arranged, an amplifying means for accumulating charges according to an electric signal output from the switching element, and outputting an electric signal obtained by amplifying the accumulated electric charge, and other than reading out charges In the non-image reading, a detecting means for detecting an electric signal output from the amplifying means when the switching element is turned on / off, and an on / off timing of the switching element at the time of reading the charge based on a detection result of the detecting means, and Control means for controlling at least one of the energies for turning on the switching element.
  • a plurality of pixels configured to include the sensor unit and the switching element are arranged, and charges corresponding to the irradiated radiation are generated in the sensor unit, The electric charge is read by the switching element and output to the signal line.
  • the amplifying means accumulates electric charge according to the electric signal output from the switching element, and outputs an electric signal obtained by amplifying the accumulated electric charge.
  • the detecting means detects an electrical signal output from the amplifying means when the switching element is turned on / off during non-image reading other than charge reading. That is, the occurrence of feedthrough noise is detected by detecting the output value of the amplifying means when the switching element is turned on / off during non-image reading, such as during reset.
  • the control means controls at least one of the on / off timing of the switching element and the energy for turning on the switching element when reading the electric charge based on the detection result of the detecting means. Accordingly, it is possible to reliably suppress feedthrough noise in consideration of actual element characteristic variations and dynamic changes.
  • it further comprises storage means for storing at least one control content of on / off timing and energy determined based on the detection result of the detection means, the control means according to the control content stored in the storage means at the time of reading the charge. At least one of on / off timing and energy may be controlled.
  • control means drives the switching element of the first pixel in the radiation detector to read a charge, and includes a part including the end of the first period, and another connected to the same signal line as the switching element of the first pixel You may make it control the switching element of each pixel so that it may have an overlap period which overlaps with a part including the start of the 2nd period which drives the switching element which drives a 2nd pixel, and reads an electric charge.
  • control means may control at least one of the on / off timing and the energy by controlling the switching element of the pixel existing in the center of the radiation detector.
  • the detection means sets a predetermined target pixel among a plurality of pixels of the radiation detector as a detection target, and the control means determines the on / off timing of the switching elements of other pixels and the energy based on the detection result of the target pixel. At least one may be determined by interpolation calculation.
  • the detection by the detection means and the control by the control means at least one timing when a predetermined temperature change is detected by the temperature detection means for detecting the temperature of the radiation detector and when a predetermined time has elapsed. May be performed. Further, the control unit compares the detection result of the detection unit with a predetermined reference value for the detection result of the detection unit for each block obtained by dividing the radiation detector into a plurality of blocks, and based on the comparison result, At least one of on / off timing and energy may be controlled.
  • detection by the detection means and control by the control means may be performed.
  • detection by the detection unit and control by the control unit may be prohibited.
  • the electric signal is detected by the detection means while changing the on / off timing or energy, and the control means reads the electric charge so that the detection result of the detection means becomes a minimum value or a value within a predetermined allowable range. At least one of on / off timing and energy may be controlled.
  • the present invention may be a radiographic image capturing system including the above-described radiographic image capturing device and radiation irradiating means for irradiating a radiation detector via a subject.
  • the control method of the radiographic imaging apparatus of the present invention includes a sensor unit that generates a charge corresponding to the irradiated radiation, and a switching element that reads the charge generated by the sensor unit and outputs it to a signal line.
  • Radiation imaging apparatus comprising: a radiation detector in which a plurality of arranged pixels are arranged; and an amplifying means for accumulating charges corresponding to the electric signals output from the switching elements and outputting electric signals obtained by amplifying the accumulated charges.
  • the detection step of detecting the electric signal output from the amplification unit when the switching element is turned on / off by the detection unit, and the charge based on the detection result of the detection step ON / OFF timing of the switching element when reading out and at least energy for turning on the switching element One of and a control step of controlling by the control means.
  • the radiographic image capturing apparatus reads a sensor unit that generates electric charge according to irradiated radiation, and reads out the electric charge generated by the sensor unit and outputs it to a signal line.
  • a radiation detector in which a plurality of pixels each including a switching element are arranged; an amplifying unit that accumulates electric charge according to an electric signal output from the switching element; and outputs an electric signal obtained by amplifying the accumulated electric charge;
  • the electric signal output from the amplifying unit is detected by the detecting unit when the switching element is turned on / off during non-image reading other than the charge reading.
  • control step based on the detection result of the detection step, at least one of the on / off timing of the switching element when reading the charge and the energy for turning on the switching element is controlled by the control means. Accordingly, it is possible to reliably suppress feedthrough noise in consideration of actual element characteristic variations and dynamic changes.
  • the radiographic apparatus further includes storage means for storing at least one control content of on / off timing and energy determined based on the detection result of the detection means, and the control step stores the charge in the storage means when reading out the charge. According to the control content, at least one of the on / off timing and the energy may be controlled.
  • control step may include a part including the end of the first period in which the switching element of the first pixel in the radiation detector is driven to read out the charge, and another connected to the same signal line as the switching element of the first pixel.
  • the driving of the switching element of each pixel may be controlled by the control means so as to have an overlapping period that overlaps a part including the start of the second period in which the switching element for driving the second pixel is driven to read out the charge. Good.
  • the switching element of the pixel existing in the center of the radiation detector may be controlled, and at least one of on / off timing and energy may be controlled by the control means.
  • a predetermined target pixel among the plurality of pixels of the radiation detector is set as a detection target of the detection unit, and the control step determines on / off timing of switching elements of other pixels based on the detection result of the target pixel. And at least one of the energy may be determined by an interpolation operation.
  • the detection step and the control step are executed at least at one timing when a predetermined temperature change is detected by the temperature detection means for detecting the temperature of the radiation detector and when a predetermined time has elapsed. It may be. Further, the control step compares the detection result of the detection means with a predetermined reference value for the detection result of the detection means for each block in which the radiation detector is divided into a plurality of blocks, and based on the comparison result, At least one of on / off timing and energy may be controlled.
  • the detection step and the control step may be executed. Further, in the case of positioning moving image shooting when the subject is positioned at a predetermined shooting position or timing moving image shooting for matching the breathing timing, the execution of the detection step and the control step may be prohibited.
  • the electrical signal is detected in the detection step while changing the on / off timing or energy, and the control step is performed when the charge is read so that the detection result of the detection step becomes a minimum value or a value within a predetermined allowable range. At least one of on / off timing and energy may be controlled.
  • this invention is good also as a radiographic imaging program for functioning a computer as a detection means and a control means in the above-mentioned radiographic imaging apparatus.
  • the present invention has an excellent effect that feed-through noise can be reliably suppressed in consideration of actual device characteristic variations and dynamic changes.
  • FIG. 1 It is a block diagram which shows the structure of the radiation information system which concerns on embodiment. It is a side view which shows an example of the arrangement
  • (A) is a cross-sectional schematic diagram which shows schematic structure of 4 pixel parts of the radiation detector which concerns on embodiment
  • (B) is a figure which shows the electrical structure of the pixel part of a radiation detector. It is a figure which shows schematic structure of the signal processing part of the radiation detector which concerns on embodiment.
  • FIG. 1 It is a figure which shows the gate on-off waveform and the output waveform of a charge amplifier.
  • A is a schematic diagram showing an image of dividing a block
  • B is a diagram showing an example in which the feedthrough noise increases as the total distance between the gate wiring and the data wiring becomes longer
  • C shows the temperature and feedthrough.
  • It is a figure which shows the relationship of the time constant of noise.
  • It is a flowchart which shows the electronic cassette control routine which concerns on embodiment of this invention. It is a timing chart which shows the example of cancellation of rising FTN and falling FTN in an overlap period.
  • It is a figure which shows the structural example provided with the dummy pixel line.
  • It is a figure which shows the structural example provided with the dummy sub pixel.
  • 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. 5). 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. 5) 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.
  • the space in front of the standing table 34 is set as the imaging position of the subject 38 when performing radiography in the standing position, and the upper space of the prone table 36 is used in performing radiography in the prone position. This is the imaging position of the subject 40.
  • 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 of the pixel portion of the radiation detector 26. It is a figure which shows an electrical structure.
  • 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 a signal output is performed.
  • the pixel group of the TFT substrate 74 is configured by the unit 52 and the sensor unit 54. 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 a thing. 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 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 absorbs light emitted from the scintillator 56 and generates electric charges. It is composed of an organic photoelectric conversion material.
  • 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, and includes a capacitor 70 that accumulates the electric charge transferred to the lower electrode 62, and a field effect as a switching element that converts the electric charge accumulated in the capacitor 70 into an electric signal and outputs the electric signal.
  • a thin film transistor (Thin Film Transistor, hereinafter may be 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 unit 52 in the pixels arranged in a matrix is extended in a certain direction (row direction), and a plurality of gates for turning on and off the thin film transistors 72 of the individual pixels.
  • a plurality of data wirings D are provided for reading the accumulated charges from the capacitor 70 via the thin film transistor 72 that is turned on and extends in a direction orthogonal to the wiring G and the gate wiring G.
  • 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 portion 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.
  • the cassette control unit 69 functions as a control unit, a detection unit, and a storage unit in the present invention.
  • 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 diagram showing a schematic configuration of a signal processing unit of the radiation detector 26 according to the present exemplary embodiment.
  • 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 (amplifying means), a sample hold circuit 76, a CDS (Correlated Double Sampling) 77, and an A / D converter 78.
  • 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 76, and output to the A / D converter 78 via the CDS 77. .
  • An analog signal is converted into a digital signal 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 signal transmitted through each data line D is 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 and hold circuit 76 is converted into an analog voltage and sequentially input to the A / D converter 78 via the CDS 77, and converted into digital image information by the A / D converter 78.
  • the digital image information converted by the A / D converter 78 is input to the cassette control unit 69 and sequentially sent from the cassette control unit 69 to the image processing control unit 102 described later.
  • the cassette control unit 69 controls the gate line driver 71 to control the on / off of the thin film transistor 72 and the on / off of the reset switch 79 of the charge amplifier 75.
  • FIG. 5 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 the radiation X from the radiation irradiation source 22A of the radiation irradiation control unit 22 based on the received irradiation conditions. Take control.
  • a plurality of gate lines for turning on and off the thin film transistor 72 of the TFT substrate and a pixel in which the thin film transistor 72 is turned on are used. Since a plurality of data lines that transmit the signal charges are crossed and arranged, when the thin film transistor 72 is turned on and off, the voltage applied to the parasitic capacitance existing at the intersection of the gate line connected to the thin film transistor 72 and the data line Changes, a noise component called so-called feedthrough noise is superimposed on the charge transmitted through the data line.
  • the feedthrough noise is generated when the thin film transistor 72 is turned on and off, and can be canceled by setting the integration period of the charge amplifier 75 so as to include each of them. Since the through-noise is large (particularly in the case of moving images, the signal charge is smaller than the still image and the ratio of feed-through noise is large), the integrated charge saturation occurs due to the feed-through noise during the integration period of the charge amplifier 75. , Feedthrough noise may not be accurately eliminated.
  • a thin film transistor 72 that drives a thin film transistor 72 that drives a thin film transistor 72 of a certain pixel and reads another charge and that drives another pixel connected to the same data line D as the certain pixel is provided.
  • the drive timing of the thin film transistor 72 of each pixel is controlled so as to have an overlapping period that overlaps with a part including the start of the readout period for driving and reading out charges. That is, feedthrough noise is generated when a gate of a certain pixel is turned off, but reverse feedthrough noise is generated when a gate of another pixel connected to the same data line D as a certain pixel is turned on. In this case, the feedthrough noise is immediately canceled in the overlap period, and it becomes possible to avoid saturation of the integrated charge.
  • the cassette control unit has an overlapping period in which the end part of the gate on / off period of the pixel Gn-1 and the start part of the gate on / off period of the pixel Gn of the next line sequentially overlap.
  • the gate line driver 71 is controlled by 69.
  • the feedthrough noise (falling FTN) when the gate of the pixel Gn-1 is turned off and the feedthrough noise (rising FTN) when the gate of the pixel Gn is turned on cancel each other out during the integration period of the charge amplifier 75. It is possible to prevent the saturation of the integrated charge due to the rapid rise FTN.
  • the feedthrough noise has a rising FTN when the gate is turned on and a falling FTN when the gate is turned off.
  • the cassette control unit 69 monitors the output of the charge amplifier 75 when the gate is turned on and when the gate is turned off when the thin film transistor 72 is turned on and off to detect the state of the feedthrough noise. .
  • the magnitude of the feedthrough noise and the time constant can be known, so that the output of the charge amplifier 75 is set to the cassette control unit 69 when the charge is reset.
  • the rising FTN occurs steeper than the falling FTN and occurs for a shorter period than the falling FTN.
  • the falling FTN occurs with a reverse polarity more slowly than the rising FTN and occurs for a longer period than the rising FTN, but the total charge amount of each feedthrough noise is the same.
  • the occurrence state of the falling FTN and the rising FTN is detected at the time of charge reset, and the gate on / off timing is controlled based on the detection result. ing.
  • the gate timing is controlled in accordance with the occurrence state of feedthrough noise, so even if the occurrence state (magnitude, time constant, etc.) of the feedthrough noise changes, the falling FTN and the rising FTN reliably cancel each other. It is supposed to be.
  • the gate on / off timing is controlled, but the time constant and the magnitude of the feedthrough noise change by changing the magnitude (energy) of the gate on voltage, so the gate on energy is controlled. You may do it.
  • both gate on / off timing and gate on energy may be controlled.
  • the output voltage of the charge amplifier 75 is monitored while shifting the on / off timing of the thin film transistor 72 at the time of charge reset. That is, in this embodiment, a part including the end of the gate on / off period of a certain pixel overlaps with a part including the start of the gate on / off period of another pixel connected to the same data wiring D as the certain pixel. Since there are overlapping periods, the feed-through noise when the gate is turned off and the feed-through noise when the gate is turned on cancel each other out in the output value of the charge amplifier 75 when the charge is reset. When the gate on / off timing is set so that the generation periods of both feedthrough noises overlap with each other, the output value of the charge amplifier 75 becomes the smallest value.
  • the cassette control unit 69 monitors the output value of the charge amplifier 75 while shifting the gate on / off timing at the time of reset, and adjusts to the gate on / off timing at which the output value of the charge amplifier 75 is the smallest.
  • Store in the cassette control unit 69 thereby, at the time of actual photographing, by controlling the gate on / off timing based on the stored control contents, the fall FTN of a certain pixel and the rise FTN of another pixel connected to the same data wiring D as the certain pixel are used. Since the feedthrough noise is surely canceled, the feedthrough noise can be suppressed.
  • the gate on / off timing may be adjusted so that the output value of the charge amplifier 75 is a value within a predetermined allowable range.
  • the voltage value may be monitored as it is, but the gain may be changed to increase the feedthrough noise for monitoring.
  • only the on / off timing may be shifted, or only one of the on / off timings may be shifted.
  • the area for adjusting the feed-through noise monitor and gate on / off timing may be adjusted over the entire surface of the two-dimensional array, but the center of the imaging area (a predetermined area in the vicinity of the center in the imaging area). ) As the target region. Considering the processing load for monitoring the feedthrough noise and adjusting the gate timing, it is preferable to match the on / off timing with the thin film transistor 72 of the pixel existing in the center of the imaging region as the control target.
  • the feed-through noise of a target pixel (for example, several pixels) determined in advance in the imaging area is monitored during non-imaging (non-image reading), and the control contents of the adjustment result by adjusting the gate on / off timing May be stored in the cassette control unit 69, and the other pixels may be adjusted by determining the gate on / off timing using interpolation calculation based on the stored control content.
  • the feedthrough noise monitoring and the gate on / off timing adjustment may be performed when a temperature change is detected by providing a temperature sensor or the like. You may make it perform every fixed time. That is, the feedthrough noise may be monitored and the gate on / off timing may be adjusted when a temperature change is detected and / or when at least one time has elapsed.
  • the feedthrough noise is divided into predetermined blocks and the feedthrough noise at the gate voltage and temperature at the time of reading is divided.
  • a default gate on / off timing determined from the size and time constant may be provided for each block.
  • the gate on / off timing may be adjusted for a block that exceeds a predetermined threshold by comparing the table value with the monitored value.
  • a different threshold may be adopted for each block.
  • the threshold of the central region is set to be stricter than other regions (adjusted if there is a difference from the default value even a little). You may make it do.
  • the threshold value may be dynamically changed by comparing the predicted value of the signal amount with the table value. For example, when the dose is lower than a predetermined dose, the threshold value may be dynamically switched such that the threshold value is tightened. Further, when handling each block in this way, a difference (for example, the current monitoring result and the previous monitoring result) from the past feedthrough noise monitoring result is obtained for each block, and the obtained difference is determined in advance. If the threshold is equal to or greater than the threshold, control may be performed by shifting from a default value (predetermined gate on / off timing).
  • the above table can be created from offset images by intentionally shifting the gate on / off overlap period.
  • the feedthrough noise generally increases as the total distance between the gate wiring G and the data wiring D is longer.
  • the block A has greater feedthrough noise than the block B.
  • the leakage current of the TFT thin film transistor 72 increases as the temperature rises, the time constant of the feedthrough noise tends to decrease as shown in FIG. 8C. Based on this, the adjustment value of the gate on / off timing may be corrected.
  • the block may have a central area of the photographing area as another block.
  • the block may be a gate IC unit constituting the gate line driver or a reading IC unit.
  • FIG. 9 is a flowchart showing a flow of an example of an electronic cassette control routine.
  • step 200 it is determined by the cassette control unit 69 whether or not it is the feedthrough noise (FTN) monitoring timing. If the determination is affirmative, the process proceeds to step 202. If the determination is negative, the process proceeds to step 212. To do. The determination may be performed, for example, by determining whether or not a predetermined time has elapsed. When a temperature sensor is provided, it is determined whether or not there has been a temperature change equal to or higher than a predetermined temperature. Alternatively, it may be determined whether it is the charge reset timing. Further, as described above, when handling each block, it is determined whether or not the difference (difference between the previous monitoring result and the current monitoring result) is greater than or equal to a predetermined threshold value for each block. Good.
  • FTN feedthrough noise
  • step 204 the cassette control unit 69 controls the gate line driver 71 so that the gate of the thin film transistor 72 is turned on and off to reset the charge, and the process proceeds to step 206.
  • step 206 the output value of the charge amplifier 75 during charge reset is detected by the cassette control unit 69, and the process proceeds to step 208.
  • step 208 it is determined whether or not the gate on / off timing of the thin film transistor 72 needs to be adjusted. The determination is made, for example, by determining whether or not the output value of the charge amplifier 75 is outside a predetermined allowable range. If the determination is affirmative, the process proceeds to step 208. If the determination is negative, step 210 is performed. Migrate to
  • step 208 the gate on / off timing is changed, the process returns to step 202, and the above-described processing is repeated.
  • step 210 the gate on / off timing is adjusted based on the monitoring result of the feedthrough noise, and the process proceeds to step 212.
  • the output of the charge amplifier 75 is monitored while shifting the gate on / off timing, and the gate on / off timing is adjusted so that the output value of the charge amplifier 75 becomes a minimum value or a value within a predetermined allowable range.
  • the control content of the adjustment result is stored in the cassette control unit 69, and the gate on / off timing is controlled based on the control content stored at the time of reading the charge at the time of capturing the frame.
  • step 212 it is determined by the cassette control unit 69 whether or not the frame is taken in. If the determination is negative, the process returns to step 200 and the above processing is repeated, and if the determination is affirmative, the process returns to step 214. Transition.
  • step 214 gradation signals for one frame are sequentially read, and the process proceeds to step 216. That is, on / off of the gate of the thin film transistor 72 is controlled according to the gate on / off timing adjusted in step 210, and the gradation signals are sequentially read out. Accordingly, the gradation signal in which the feedthrough noise is surely canceled in the overlap period by the falling FTN of a certain pixel and the rising FTN of another pixel connected to the same data line D as the certain pixel, thereby suppressing the feedthrough noise. Can be obtained. For example, as shown in FIG.
  • step 216 it is determined whether or not the photographing is finished. If the determination is negative, the process returns to step 214 and the above-described processing is repeated. When the determination is affirmed, the series of processing ends.
  • the gate on / off timing may be adjusted according to the feedthrough noise monitoring result.
  • the gate on / off timing adjustment method may be changed according to the feedthrough noise monitoring result according to the frame rate. For example, since a sufficient integration time can be obtained at a predetermined low frame rate, it is possible to cancel feedthrough noise without precisely matching the gate on / off timing. You may make it change with frame rates.
  • the gate on time may be controlled to be sufficiently long for a low frame rate, short for the high frame rate, and short for the above overlap period.
  • the cassette control unit 69 may control not to adopt the image as a dummy line.
  • the feedthrough noise of the charge amplifier output 75 is monitored while shifting the gate on / off timing at the time of reset so that the charge amplifier output becomes the minimum value (or a value within a predetermined allowable range).
  • the gate on / off timing is adjusted.
  • the magnitude and time constant of the feedthrough noise at reset are monitored, and the gate on / off timing or gate on voltage is adjusted based on the magnitude and time constant of the feedthrough noise. May be. In this case, monitoring of the magnitude of feedthrough noise and the time constant may be obtained from the output of the charge amplifier 75.
  • the charge amplifier 75 may be adjusted so that the peak of the falling FTN and the rising FTN are within the integration time of the charge amplifier 75, or may be adjusted so that the half value is entered. Alternatively, adjustment may be made so that 3 ⁇ is included.
  • the case where the feedthrough noise is suppressed by controlling the drive timing of the thin film transistor 72 of each pixel so as to have an overlapping period that overlaps with a part including the start of the readout period for reading the charge by driving the signal is not limited to this.
  • a configuration including a dummy pixel line that includes a thin film transistor 112 and a capacitor 114 and does not generate signal charges is used to monitor feedthrough noise during charge reset.
  • the gate-on voltage or the like of the thin film transistor 72 may be adjusted according to the monitoring result.
  • a second gate line driver 116 for controlling on / off of the thin film transistor 112 of the dummy pixel is further provided for the present embodiment, and as shown in FIG.
  • the feed-through noise is canceled by turning off the thin film transistor 112 of the dummy pixel when turning on, and turning off the thin film transistor 112 of the dummy pixel when turning off the thin film transistor 72 for image reading.
  • the configuration of the above-described dummy pixel line in FIG. 11A is provided for each pixel, that is, a thin film transistor 112 and a capacitor 114 are further provided for each pixel of this embodiment mode.
  • the feed-through noise at the time of charge reset is monitored, and the gate of the thin film transistor 112 for image reading is turned on according to the monitor result.
  • the voltage or the like may be adjusted.

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Abstract

La présente invention a pour but de réduire de manière fiable un bruit de traversée, en prenant en considération un mauvais alignement de caractéristique et un changement dynamique d'éléments réels. Tout en faisant varier la temporisation de marche/arrêt de grille à un instant de réinitialisation, une unité de commande de cartouche (69) surveille une valeur de sortie (détection de FTN) d'un amplificateur de charge (75), et sur la base du résultat de la surveillance, commande un pilote de ligne de grille (71), ajustant soit la temporisation de marche/arrêt de grille d'un transistor en couches minces (72), soit l'énergie d'une tension de marche de grille, etc. A titre d'exemple, un ajustement est réalisé de telle sorte que la valeur de sortie de l'amplificateur de charge (75) atteint soit la temporisation de marche/arrêt de grille la plus petite soit la tension de marche de grille la plus petite.
PCT/JP2013/074324 2012-09-25 2013-09-10 Dispositif de radiographie, système de radiographie, procédé de commande de dispositif de radiographie et programme de radiographie WO2014050532A1 (fr)

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JP2004037382A (ja) * 2002-07-05 2004-02-05 Toshiba Corp 放射線検出器及び放射線診断装置
JP2004147102A (ja) * 2002-10-24 2004-05-20 Sharp Corp 画像読み取り装置および画像読み取り方法
JP2005019537A (ja) * 2003-06-24 2005-01-20 Hamamatsu Photonics Kk 時間分解測定装置
JP2008154957A (ja) * 2006-12-26 2008-07-10 Canon Inc 撮像装置及びその駆動方法
JP2008167846A (ja) * 2007-01-10 2008-07-24 Toshiba Corp Ｘ線透過像表示システム
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Publication number Priority date Publication date Assignee Title
JP2003274292A (ja) * 2002-03-14 2003-09-26 Sony Corp 固体撮像装置およびその駆動方法
JP2004037382A (ja) * 2002-07-05 2004-02-05 Toshiba Corp 放射線検出器及び放射線診断装置
JP2004147102A (ja) * 2002-10-24 2004-05-20 Sharp Corp 画像読み取り装置および画像読み取り方法
JP2005019537A (ja) * 2003-06-24 2005-01-20 Hamamatsu Photonics Kk 時間分解測定装置
JP2008154957A (ja) * 2006-12-26 2008-07-10 Canon Inc 撮像装置及びその駆動方法
JP2008167846A (ja) * 2007-01-10 2008-07-24 Toshiba Corp Ｘ線透過像表示システム
JP2009212618A (ja) * 2008-02-29 2009-09-17 Fujifilm Corp 画像検出装置
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