WO2011092981A1 - Dispositif de prise d'images radiographiques et système de prise d'images radiographiques - Google Patents

Dispositif de prise d'images radiographiques et système de prise d'images radiographiques Download PDF

Info

Publication number
WO2011092981A1
WO2011092981A1 PCT/JP2010/073136 JP2010073136W WO2011092981A1 WO 2011092981 A1 WO2011092981 A1 WO 2011092981A1 JP 2010073136 W JP2010073136 W JP 2010073136W WO 2011092981 A1 WO2011092981 A1 WO 2011092981A1
Authority
WO
WIPO (PCT)
Prior art keywords
radiation
voltage
detection element
radiation detection
reset process
Prior art date
Application number
PCT/JP2010/073136
Other languages
English (en)
Japanese (ja)
Inventor
史景 内田
剛 齋藤
友則 駒坂
Original Assignee
コニカミノルタエムジー株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by コニカミノルタエムジー株式会社 filed Critical コニカミノルタエムジー株式会社
Priority to JP2011551712A priority Critical patent/JP5621788B2/ja
Publication of WO2011092981A1 publication Critical patent/WO2011092981A1/fr

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4283—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by a detector unit being housed in a cassette
    • 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
    • H04N25/60—Noise processing, e.g. detecting, correcting, reducing or removing noise
    • H04N25/65—Noise processing, e.g. detecting, correcting, reducing or removing noise applied to reset noise, e.g. KTC noise related to CMOS structures by techniques other than CDS

Definitions

  • the present invention relates to a radiographic image capturing apparatus and a radiographic image capturing system, and more particularly to a radiographic image capturing apparatus that resets each radiation detection element before capturing a radiographic image and a radiographic image capturing system using the same.
  • a so-called direct type radiographic imaging device that generates electric charges by a detection element in accordance with the dose of irradiated radiation such as X-rays and converts it into an electrical signal, or other radiation such as visible light with a scintillator or the like.
  • Various so-called indirect radiographic imaging devices have been developed that convert charges to electromagnetic waves after being converted into electrical signals by generating electric charges with photoelectric conversion elements such as photodiodes in accordance with the energy of the converted and irradiated electromagnetic waves. Yes.
  • the detection element in the direct type radiographic imaging apparatus and the photoelectric conversion element in the indirect type radiographic imaging apparatus are collectively referred to as a radiation detection element.
  • This type of radiographic imaging device is known as an FPD (Flat Panel Detector) and has been conventionally formed integrally with a support base (or a bucky apparatus) (see, for example, Patent Document 1).
  • FPD Full Panel Detector
  • a portable radiographic imaging device in which an element or the like is housed in a housing has been developed and put into practical use (see, for example, Patent Documents 2 and 3).
  • radiographic imaging when radiographic imaging is performed by exposing radiation from a radiation generating apparatus in a state where the radiographic imaging apparatus is not in a state suitable for imaging, a radiographic image obtained by radiographic imaging is obtained. May be unusable due to the degradation of image quality. Therefore, re-imaging is necessary. For example, when a radiographic imaging apparatus is used to capture a radiographic image for medical use, radiation is again applied to the patient as a subject, and the patient's The exposure dose increases, which is not preferable.
  • the radiation generator is interlocked so that, for example, even if an operator such as a radiologist presses the exposure switch of the radiation generator, the radiation is not exposed alone.
  • an interlock release signal a signal indicating that the interlock is released (hereinafter referred to as an interlock release signal) is output to enable radiation exposure.
  • the technique of doing is known (for example, refer patent document 4).
  • each radiation detection element for example, as shown in FIG. 7 to be described later, an on-voltage is applied to each of the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving unit 15, and the scanning line 5
  • Each thin film transistor (Thin Film Transistor, hereinafter referred to as TFT) 8 which is a switching means in which a gate electrode 8g (denoted as G in the figure) is connected to each of the lines L1 to Lx is turned on.
  • TFT Thin Film Transistor
  • the reset processing of each radiation detection element is performed by sequentially switching the scanning line 5 for switching the voltage applied from the gate driver 15b between the on voltage and the off voltage between the lines L1 to Lx.
  • the TFTs 8 that are turned on are sequentially switched.
  • the on-voltage applied to the first line L1 of the scanning line 5 is switched to the off-voltage (indicated by the broken line in the figure).
  • the reset process during the period of time) is referred to as reset process Rm for one surface.
  • the reset process of each radiation detection element is configured such that the reset process Rm for one surface is repeatedly performed as shown in FIG.
  • irradiation start a signal indicating that the exposure switch has been pressed by an operator such as a radiation engineer from the radiation generating apparatus side to the radiographic imaging apparatus.
  • the reset process is performed by the reset process Rm for one time.
  • the amount of extra charge remaining in the radiation detection element 7 changes between the radiation detection element 7 that has been subjected to the above and the radiation detection element 7 that has not been reset.
  • each of the radiation detection elements 7 reads out the extra charge remaining in the radiation detection element 7 as described above together with the original image data. Because of the difference in the amount of charge, the radiation detection element region that has been reset and the radiation detection element region that has not been reset on the radiation image that is finally generated based on image data, etc. There may be a problem that unevenness occurs.
  • JP-A-9-73144 JP 2006-058124 A Japanese Patent Laid-Open No. 6-342099 International Publication WO2006 / 101233 JP-A-5-240960 JP-A-9-131337
  • each TFT 8 is turned off, and each radiation detection element 7 is shifted to the charge accumulation state.
  • an interlock release signal is transmitted from the radiographic imaging apparatus as soon as the exposure switch is pressed by the operator.
  • the reset process Rm for one surface for a predetermined number of times does not provide sufficient reset efficiency for each radiation detection element 7, and the radiation detection element 7 shifts to a charge accumulation state with a relatively large excess charge remaining. There is a possibility that.
  • each radiation detection is performed after radiographic imaging. Since many residual charges and dark charges are mixed in the image data read during the image data reading process from the element 7, the S / N ratio of the radiation image generated based on the image data is deteriorated. As a result, the image quality is degraded.
  • the reset process Rm for one surface is repeatedly performed in the state where the interlock is applied as described above until immediately before the radiation irradiation. It is desirable that the reset process be performed accurately. Even in such a configuration, it is desirable that the waiting time T from when the exposure switch is pressed to when the interlock is released to actually start the radiation irradiation is shortened.
  • the present invention has been made in view of the above-described problems, and performs radiographic imaging capable of transmitting an interlock release signal immediately after receiving an irradiation start signal while accurately performing reset processing of each radiation detection element.
  • An object of the present invention is to provide a radiographic imaging system capable of irradiating radiation immediately after an operator presses an exposure switch.
  • the radiographic imaging device of the present invention includes: A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; , An off state and an on state are switched according to a voltage applied to the connected scanning line, arranged for each radiation detection element, and in the off state, the charge generated in the radiation detection element is retained, Switch means for releasing the charge from the radiation detection element in the ON state; Scan driving means comprising: a gate driver that switches a voltage applied to the switch means via the scanning line between an on voltage and an off voltage; and a power supply circuit that supplies the on voltage and the off voltage to the gate driver.
  • a time interval from switching the voltage applied to each scanning line to the on-voltage to switching to the off-voltage is made shorter than the time interval before the stage to perform the reset process for the one surface, and communication means
  • the irradiation start signal is received via the gate driver, when the reset process for the one surface whose time interval is shortened is completed, an off voltage is applied to all the scanning lines from the gate driver, and each switch unit is activated.
  • An interlock release signal is transmitted through the communication means while being turned off.
  • the radiographic imaging system of the present invention is The radiographic imaging device of the present invention, A radiation generation apparatus comprising a radiation source that irradiates radiation to the radiation imaging apparatus, and an exposure switch that transmits at least an irradiation start signal when operated; With When the radiation generation device receives the irradiation start signal from the exposure switch, the radiation generation device transmits the irradiation start signal to the radiation image capturing device, and receives the interlock release signal from the radiation image capturing device. Radiation is emitted from the radiation source.
  • the radiographic imaging apparatus starts irradiation. After receiving the signal, the interlock release signal can be transmitted immediately.
  • an interlock release signal is promptly transmitted from the radiographic imaging apparatus in this way, and radiation is promptly emitted from the radiation source of the radiation generating apparatus. It becomes possible. For this reason, it is possible to shorten the waiting time from when the operator such as a radiologist presses the exposure switch until the interlock is released and radiation is actually started.
  • the image capturing system is convenient for the operator.
  • the ON time in the reset process for one surface that is repeatedly performed until the charge remaining in each radiation detection element reaches a predetermined charge amount is Since it is controlled so as to have a relatively long time interval without being shortened, excess radiation remaining inside is sufficiently discharged from each radiation detection element. Therefore, it is possible to accurately perform the reset process of each radiation detection element, and to accurately prevent the residual charge from being mixed into the image data read from each radiation detection element and causing deterioration of the image quality of the radiation image. Is possible.
  • FIG. 2 is a cross-sectional view taken along line XX in FIG. It is a top view which shows the structure of the board
  • FIG. 5 is a cross-sectional view taken along line YY in FIG. It is a side view explaining the board
  • FIG. 6 is a timing chart for explaining that the on-time is shortened by reset processing for one surface in the first embodiment. It is a graph explaining that the amount of charge in each radiation detection element decreases when the reset process is repeated, but does not decrease below that when the predetermined amount of charge is reached. It is a graph explaining that the reset process for one surface where the on-time is shortened is repeatedly performed when the amount of charge in each radiation detection element becomes a predetermined amount of charge.
  • 6 is a timing chart for explaining that the waiting time is shortened because the time required for the reset process for one surface is shortened in the first embodiment. It is a timing chart explaining the interval provided between the reset processes for 1 surface in 2nd Embodiment. It is a timing chart explaining waiting time becoming short in a 2nd embodiment. It is a timing chart explaining waiting time becoming short in a 3rd embodiment. It is a timing chart explaining waiting time becoming short in a 3rd embodiment. It is a timing chart in the reset process for one surface in the conventional case. It is a timing chart explaining waiting time becoming long in the conventional case.
  • the radiographic imaging device is a so-called indirect radiographic imaging device that includes a scintillator or the like and converts the irradiated radiation into electromagnetic waves of other wavelengths such as visible light to obtain an electrical signal.
  • the present invention can also be applied to a direct radiographic imaging apparatus.
  • the radiographic image capturing apparatus is portable will be described, the present invention is also applicable to a radiographic image capturing apparatus formed integrally with a support base or the like.
  • FIG. 1 is an external perspective view of a radiographic imaging apparatus according to the first embodiment of the present invention
  • FIG. 2 is a cross-sectional view taken along line XX of FIG.
  • the radiation image capturing apparatus 1 according to the present embodiment is configured by housing a scintillator 3, a substrate 4, and the like in a housing 2.
  • the housing 2 is formed of a material such as a carbon plate or plastic that transmits at least the radiation incident surface R. 1 and 2 show a case in which the housing 2 is a so-called lunch box type formed by the frame plate 2A and the back plate 2B. However, the housing 2 is integrally formed in a rectangular tube shape. It is also possible to use a so-called monocoque type.
  • the side surface of the housing 2 is opened and closed for replacement of a power switch 36, an indicator 37 composed of LEDs and the like, and a battery 41 (not shown) (see FIG. 7 described later).
  • a possible lid member 38 and the like are arranged.
  • an antenna device 39 that is a communication unit for wirelessly transmitting and receiving image data and the like to an external device such as a console 58 (see FIG. 9) described later is embedded in the side surface of the lid member 38. It is.
  • the installation position of the antenna device 39 is not limited to the side surface portion of the lid member 38, and the antenna device 39 can be installed at an arbitrary position of the radiographic image capturing apparatus 1.
  • the number of antenna devices 39 to be installed is not limited to one, and a plurality of antenna devices 39 may be provided.
  • a communication means for example, as a communication means, a LAN (Local Area Network) cable, a USB (Universal Serial Bus) cable, etc. Are connected to the side surface of the radiation imaging apparatus 1.
  • a base 31 is disposed inside the housing 2 via a lead thin plate (not shown) on the lower side of the substrate 4, and an electronic component 32 and the like are disposed on the base 31.
  • the PCB substrate 33, the buffer member 34, and the like are attached.
  • a glass substrate 35 for protecting the substrate 4 and the radiation incident surface R of the scintillator 3 is disposed.
  • the scintillator 3 is affixed to a detection part P (described later) of the substrate 4.
  • the scintillator 3 is, for example, a phosphor whose main component is converted into an electromagnetic wave having a wavelength of 300 to 800 nm, that is, an electromagnetic wave centered on visible light when it receives radiation, and that is output.
  • the substrate 4 is formed of a glass substrate. As shown in FIG. 3, a plurality of scanning lines 5 and a plurality of signal lines are provided on a surface 4 a of the substrate 4 facing the scintillator 3. 6 are arranged so as to cross each other. In each small region r defined by the plurality of scanning lines 5 and the plurality of signal lines 6 on the surface 4 a of the substrate 4, radiation detection elements 7 are respectively provided.
  • the region is a detection unit P.
  • a photodiode is used as the radiation detection element 7, but other than this, for example, a phototransistor or the like can also be used.
  • Each radiation detection element 7 is connected to the source electrode 8s of the TFT 8 serving as a switch means, as shown in the enlarged views of FIGS.
  • the drain electrode 8 d of the TFT 8 is connected to the signal line 6.
  • the TFT 8 is turned on when a turn-on voltage is applied to the connected scanning line 5 by the scanning drive means 15 described later, and is applied to the gate electrode 8g, and is stored in the radiation detection element 7. The electric charge that is present is emitted to the signal line 6. Further, the TFT 8 is turned off when the off voltage is applied to the connected scanning line 5 and the off voltage is applied to the gate electrode 8g, and the emission of the charge from the radiation detecting element 7 to the signal line 6 is stopped. The charges generated in the radiation detection element 7 are held and accumulated in the radiation detection element 7.
  • FIG. 5 is a sectional view taken along line YY in FIG.
  • a gate electrode 8g of a TFT 8 made of Al, Cr or the like is formed on the surface 4a of the substrate 4 so as to be integrally laminated with the scanning line 5, and silicon nitride (laminated on the gate electrode 8g and the surface 4a).
  • An upper portion of the gate electrode 8g on the gate insulating layer 81 made of SiN x ) or the like is connected to the first electrode 74 of the radiation detection element 7 via a semiconductor layer 82 made of hydrogenated amorphous silicon (a-Si) or the like.
  • the formed source electrode 8s and the drain electrode 8d formed integrally with the signal line 6 are laminated.
  • the source electrode 8s and the drain electrode 8d are divided by a first passivation layer 83 made of silicon nitride (SiN x ) or the like, and the first passivation layer 83 covers both electrodes 8s and 8d from above.
  • ohmic contact layers 84a and 84b formed in an n-type by doping hydrogenated amorphous silicon with a group VI element are stacked between the semiconductor layer 82 and the source electrode 8s and the drain electrode 8d, respectively.
  • the TFT 8 is formed as described above.
  • an auxiliary electrode 72 is formed by laminating Al, Cr, or the like on the insulating layer 71 formed integrally with the gate insulating layer 81 on the surface 4 a of the substrate 4.
  • a first electrode 74 made of Al, Cr, Mo or the like is laminated on the auxiliary electrode 72 with an insulating layer 73 formed integrally with the first passivation layer 83 interposed therebetween.
  • the first electrode 74 is connected to the source electrode 8 s of the TFT 8 through the hole H formed in the first passivation layer 83.
  • a p layer 77 formed by doping a group III element into silicon and forming a p-type layer is formed by laminating sequentially from below.
  • the radiation incident surface R of the housing 2 of the radiographic imaging apparatus 1 At the time of radiographic imaging, radiation enters from the radiation incident surface R of the housing 2 of the radiographic imaging apparatus 1 and is converted into electromagnetic waves such as visible light by the scintillator 3, and the converted electromagnetic waves are irradiated from above in the figure. Then, the electromagnetic wave reaches the i layer 76 of the radiation detection element 7, and electron-hole pairs are generated in the i layer 76. In this way, the radiation detection element 7 converts the electromagnetic waves irradiated from the scintillator 3 into electric charges.
  • a second electrode 78 made of a transparent electrode such as ITO is laminated and formed so that the irradiated electromagnetic wave reaches the i layer 76 and the like.
  • the radiation detection element 7 is formed as described above. The order of stacking the p layer 77, the i layer 76, and the n layer 75 may be reversed. Further, in the present embodiment, a case where a so-called pin-type radiation detection element formed by sequentially stacking the p layer 77, the i layer 76, and the n layer 75 as described above is used as the radiation detection element 7. However, it is not limited to this.
  • a bias line 9 for applying a bias voltage to the radiation detection element 7 is connected to the upper surface of the second electrode 78 of the radiation detection element 7 via the second electrode 78.
  • the second electrode 78 and the bias line 9 of the radiation detection element 7, the first electrode 74 extended to the TFT 8 side, the first passivation layer 83 of the TFT 8, that is, the upper surfaces of the radiation detection element 7 and the TFT 8 are A second passivation layer 79 made of silicon nitride (SiN x ) or the like is covered from above.
  • one bias line 9 is connected to a plurality of radiation detection elements 7 arranged in rows, and each bias line 9 is connected to a signal line 6. Are arranged in parallel with each other. Further, each bias line 9 is bound to the connection 10 at a position outside the detection portion P of the substrate 4.
  • each scanning line 5, each signal line 6, and connection 10 of the bias line 9 are input / output terminals (also referred to as pads) provided near the edge of the substrate 4. 11 is connected.
  • each input / output terminal 11 is provided with a COF (Chip On Film) 12 in which a chip such as a gate IC 12a constituting a gate driver 15b of the scanning drive means 15 described later is formed on a film. They are connected via an anisotropic conductive adhesive material 13 such as an anisotropic conductive adhesive film (Anisotropic Conductive Film) or an anisotropic conductive paste (Anisotropic Conductive Paste).
  • an anisotropic conductive adhesive material 13 such as an anisotropic conductive adhesive film (Anisotropic Conductive Film) or an anisotropic conductive paste (Anisotropic Conductive Paste).
  • the COF 12 is routed to the back surface 4b side of the substrate 4 and connected to the PCB substrate 33 described above on the back surface 4b side.
  • substrate 4 part of the radiographic imaging apparatus 1 is formed.
  • illustration of the electronic component 32 and the like is omitted.
  • FIG. 7 is a block diagram illustrating an equivalent circuit of the radiographic imaging apparatus 1 according to the present embodiment
  • FIG. 8 is a block diagram illustrating an equivalent circuit for one pixel constituting the detection unit P.
  • each radiation detection element 7 of the detection unit P of the substrate 4 has the bias line 9 connected to the second electrode 78, and each bias line 9 is bound to the connection 10 to the bias power supply 14. It is connected.
  • the bias power supply 14 applies a bias voltage to the second electrode 78 of each radiation detection element 7 via the connection 10 and each bias line 9.
  • the bias power source 14 is connected to a control unit 22 described later, and the control unit 22 controls a bias voltage applied to each radiation detection element 7 from the bias power source 14.
  • the bias line 9 is connected via the second electrode 78 to the p-layer 77 side (see FIG. 5) of the radiation detection element 7.
  • the bias power supply 14 supplies a voltage equal to or lower than a voltage applied to the second electrode 78 of the radiation detection element 7 via the bias line 9 as a bias voltage on the first electrode 74 side of the radiation detection element 7 (that is, a so-called reverse bias voltage). Is applied.
  • the first electrode 74 of each radiation detection element 7 is connected to the source electrode 8s of the TFT 8 (indicated as S in FIGS. 7 and 8), and the gate electrode 8g of each TFT 8 (FIGS. 7 and 8). Are respectively connected to the lines L1 to Lx of the scanning line 5 extending from a gate driver 15b of the scanning driving means 15 described later. Further, the drain electrode 8 d (denoted as D in FIGS. 7 and 8) of each TFT 8 is connected to each signal line 6.
  • the scan driver 15 includes a power supply circuit 15a for supplying an on voltage and an off voltage to the gate driver 15b via the wiring 15c, and a voltage to be applied to each line L1 to Lx of the scan line 5 between the on voltage and the off voltage.
  • a gate driver 15b that switches between the on state and the off state of each TFT 8 is provided.
  • the gate driver 15b applies the pulse width of the on-voltage when applying the on-voltage to each of the lines L1 to Lx of the scanning line 5 based on a trigger signal transmitted from the control unit 22 described later. That is, the time interval from when the voltage applied to each of the lines L1 to Lx of the scanning line 5 is switched from the off voltage to the on voltage until the voltage is switched again to the off voltage (that is, the on time described later) is changed by pulse width modulation (Pulse Width). It is configured to be modulated by Modulation (PWM) or the like.
  • PWM Pulse Width
  • each signal line 6 is connected to each readout circuit 17 formed in the readout IC 16.
  • the readout IC 16 is provided with one readout circuit 17 for each signal line 6.
  • the readout circuit 17 includes an amplification circuit 18 and a correlated double sampling circuit 19.
  • An analog multiplexer 21 and an A / D converter 20 are further provided in the reading IC 16. 7 and 8, the correlated double sampling circuit 19 is represented as CDS. In FIG. 8, the analog multiplexer 21 is omitted.
  • the amplifier circuit 18 is configured by a charge amplifier circuit, and is configured by connecting a capacitor 18b and a charge reset switch 18c in parallel to the operational amplifier 18a and the operational amplifier 18a, respectively.
  • a power supply unit 18 d for supplying power to the amplifier circuit 18 is connected to the amplifier circuit 18.
  • the signal line 6 is connected to the inverting input terminal on the input side of the operational amplifier 18 a of the amplifier circuit 18, and the reference potential V 0 is applied to the non-inverting input terminal on the input side of the amplifier circuit 18. ing.
  • the reference potential V 0 is set to an appropriate value, and in this embodiment, for example, 0 [V] is applied.
  • the charge reset switch 18c of the amplifier circuit 18 is connected to the control means 22, and is controlled to be turned on / off by the control means 22. If the charge reset switch 18c is turned off and the TFT 8 of the radiation detection element 7 is turned on during the reading process of the image data from each radiation detection element 7, the charge released from each radiation detection element 7 is signaled. A voltage value corresponding to the amount of accumulated electric charge is output from the output side of the operational amplifier 18a by flowing into the capacitor 18b via the line 6 and accumulated therein.
  • the amplification circuit 18 outputs a voltage value according to the amount of charge output from each radiation detection element 7 and converts the charge voltage.
  • the charge reset switch 18c When the charge reset switch 18c is turned on, the input side and the output side of the amplifier circuit 18 are short-circuited, and the charge accumulated in the capacitor 18b is discharged to reset the amplifier circuit 18. ing.
  • the amplifier circuit 18 may be configured to output a current in accordance with the charge output from the radiation detection element 7.
  • a correlated double sampling circuit (CDS) 19 is connected to the output side of the amplifier circuit 18.
  • the correlated double sampling circuit 19 has a sample and hold function.
  • the sample and hold function in the correlated double sampling circuit 19 is turned on / off by a pulse signal transmitted from the control means 22. To be controlled.
  • control means 22 controls the amplification circuit 18 and the correlated double sampling circuit 19 in the process of reading image data from each radiation detection element 7 after radiographic imaging, and is emitted from each radiation detection element 7.
  • the charge is converted into a charge voltage by the amplifier circuit 18, and the voltage value after the charge voltage conversion is sampled by the correlated double sampling circuit 19 and outputted to the downstream side as image data.
  • the image data of each radiation detection element 7 output from the correlated double sampling circuit 19 is transmitted to the analog multiplexer 21 (see FIG. 7), and is sequentially transmitted from the analog multiplexer 21 to the A / D converter 20. Then, the A / D converter 20 sequentially converts the image data into digital values, which are output to the storage means 40 and sequentially stored.
  • the control means 22 includes a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), a RAM (Random Access Memory), an input / output interface connected to the bus, an FPGA (Field Programmable Gate Array), etc. It is configured. It may be configured by a dedicated control circuit. And the control means 22 controls operation
  • DRAM Dynamic RAM
  • the above-described antenna device 39 is connected to the control unit 22, and each member such as the detection unit P, the scanning drive unit 15, the readout circuit 17, the storage unit 40, the bias power supply 14, and the like.
  • a battery 41 for supplying electric power is connected.
  • the battery 41 is provided with a connection terminal 42 for charging the battery 41 by supplying power to the battery 41 from a charging device (not shown) such as a cradle.
  • control means 22 controls the bias power supply 14 to set a bias voltage to be applied to each radiation detection element 7 from the bias power supply 14, or the charge reset switch 18 c of the amplification circuit 18 of the readout circuit 17.
  • Various processes such as on / off control and transmission of a pulse signal to the correlated double sampling circuit 19 to control on / off of the sample hold function are executed.
  • control means 22 controls the scanning driving means 15 with respect to the scanning driving means 15 at the time of reset processing of each radiation detecting element 7 or at the time of reading out image data from each radiation detecting element 7 after radiographic imaging.
  • the gate driver 15b transmits a trigger signal for starting application of a voltage to be applied to the gate electrode 8g of each TFT 8 while switching the on voltage and the off voltage via the lines L1 to Lx of the scanning line 5. Yes.
  • FIG. 9 is a diagram illustrating an overall configuration of the radiographic image capturing system according to the present embodiment.
  • the radiographic imaging system 50 includes, for example, an imaging room R ⁇ b> 1 that irradiates radiation and images a subject (part of a patient to be imaged) that is a part of a patient (not shown), and a radiographer or the like.
  • the anterior chamber R2 for performing various operations such as control of the start of radiation applied to the subject by the operator, and the outside thereof are arranged.
  • a bucky device 51 that can be loaded with the radiographic imaging device 1 described above, a radiation source 52 that includes an X-ray tube (not shown) that generates radiation to irradiate a subject, and a radiation generation device 55 that controls the radiation source 52 are provided.
  • a base station 54 provided with a wireless antenna 53 that relays these communications is provided.
  • the portable radiographic imaging device 1 is used by being loaded into the cassette holding portion 51a of the bucky device 51.
  • the radiographic imaging device 1 is used as the bucky device 51. Or may be formed integrally with a support base or the like. Further, as described above, when communication between the radiographic imaging apparatus 1 and an external apparatus is performed via a cable such as a LAN cable, these cables are connected to the base station 54 as shown in FIG. It is also possible to configure such that information such as data can be transmitted / received by wired communication via a cable or the base station 54.
  • the base station 54 is connected to the radiation generating device 55 and the console 58, and signals for LAN communication when transmitting information between the radiographic image capturing device 1 and the console 58 are transmitted to the base station 54. Is converted into a signal for transmitting information to and from the radiation generating device 55, and a converter (not shown) that performs the reverse conversion is incorporated.
  • an operation console 57 of the radiation generator 55 is provided in the front chamber R2, and the operation console 57 includes a CRT (Cathode Ray Ray Tube) or an LCD for displaying information to an operator such as a radiation engineer.
  • a display unit (not shown) such as (Liquid Crystal Display) is provided.
  • the console 57 is provided with an exposure switch 56 that is operated by an operator such as a radiologist to instruct the radiation generator 55 to start radiation irradiation.
  • the exposure switch 56 includes a rod-shaped button portion 56a having a predetermined stroke and a housing that supports the button portion 56a so as to be movable in the stroke direction indicated by an arrow S in the drawing. It is comprised with the body part 56b.
  • the button part 56a of the exposure switch 56 includes, for example, a cylindrical part 56a1 protruding upward from the casing part 56b and a columnar part 56a2 protruding further upward from the inside thereof.
  • the exposure switch 56 is operated.
  • An activation signal is transmitted to the radiation generator 55 via the table 57.
  • the radiation generating device 55 places the radiation source 52 in a standby state by starting rotation of the anode of the X-ray tube of the radiation source 52.
  • the radiation generator 55 When receiving the irradiation start signal from the exposure switch 56, the radiation generator 55 transmits the irradiation start signal to the radiation image capturing apparatus 1 via the base station 54 by a wireless method or a wired method. Then, as will be described later, when receiving the interlock release signal transmitted from the radiographic imaging apparatus 1 via the base station 54, the radiation generation apparatus 55 emits radiation from the X-ray tube of the radiation source 52. It is like that.
  • the radiation generating device 55 moves the radiation source 52 to a predetermined position so that the radiation image capturing device 1 loaded in the designated bucky device 51 can be appropriately irradiated with radiation, or the radiation direction thereof. Adjusting a diaphragm (not shown) so that radiation is irradiated within a predetermined region of the radiographic imaging apparatus 1, or adjusting the radiation source 52 so that an appropriate dose of radiation is irradiated Various controls such as these are performed on the radiation source 52. In addition, you may comprise so that operators, such as a radiographer, may perform these processes manually.
  • the radiation generating device 55 receives the radiation source 52 when a predetermined time has elapsed from the start of radiation irradiation from the radiation source 52 or when a radiation irradiation end signal is transmitted from the radiation imaging apparatus 1. The irradiation of radiation from the radiation source 52 is stopped by stopping the X-ray tube.
  • the radiographic image capturing apparatus 1 may be mounted and used in the bucky device 51 as described above. In other words, it can be used alone.
  • the radiation image capturing apparatus 1 is arranged on the upper surface side in a single state, for example, in a bed provided in the imaging room R1 or in a bucky apparatus 51B for supine imaging as shown in FIG. (See FIG. 1)
  • the patient's hand which is the subject, can be placed on the top, or the patient's waist, legs, etc. lying on the bed can be inserted between the bed and the bed. It has become.
  • radiation image capturing is performed by irradiating the radiation image capturing apparatus 1 with radiation from a portable radiation source 52B or the like via a subject.
  • a console 58 constituted by a computer or the like that can process image data based on the image data transmitted from the radiation image capturing apparatus 1 and generate a final radiation image. Is provided outside the photographing room R1 and the front room R2. It is also possible to configure the console 58 so as to be provided, for example, in the front chamber R2.
  • the console 58 is connected to or includes a storage means 59 composed of an HDD (Hard Disk Drive) or the like.
  • a preview image based on image data acquired by radiographic imaging is displayed on the console 58, or the radiographic imaging apparatus 1 is set between a wake-up state and a sleep state.
  • the power switch 36 (see FIG. 1) of the radiographic image capturing apparatus 1 is pressed and activated, the state of the radiographic image capturing apparatus 1 is changed to an awake state by an instruction from the console 58, 7 or the like, the control means 22 of the radiographic image capturing apparatus 1 performs reset processing of each radiation detection element 7.
  • the radiographic imaging device 1 is used by being loaded into the bucky device 51, the radiographic imaging device 1 is loaded into the cassette holding portion 51a (see FIG. 9) of the predetermined bucky device 51.
  • the control unit 22 of the radiographic image capturing apparatus 1 performs scanning that switches the voltage applied from the gate driver 15 b of the scanning drive unit 15 between the on voltage and the off voltage.
  • the line 5 is sequentially switched, and the reset process is performed while repeatedly performing the reset process Rm for one surface.
  • the control means 22 starts from the gate driver 15b of the scanning drive means 15 to each line L1 to L4 of the scanning line 5 as in the conventional case shown in FIG.
  • the gate driver 15b scans the scanning line so that the time interval (hereinafter referred to as ON time) from when the voltage applied to Lx is switched from the OFF voltage to the ON voltage is switched to the OFF voltage again becomes a relatively long time interval.
  • the ON voltage is applied to each of the five lines L1 to Lx.
  • the gate driver 15b of the scanning drive unit 15 scans the scanning line 5 so that the on-time in the reset process Rm for one surface becomes longer at the stage where the reset process of each radiation detection element 7 is started.
  • the ON voltage pulse width for applying the ON voltage to each of the lines L1 to Lx is set to be long.
  • the control unit 22 transmits a trigger signal to the scanning driving unit 15 to start reset processing of each radiation detection element 7
  • the gate driver 15 b of the scanning driving unit 15 applies to each line L 1 to Lx of the scanning line 5.
  • the voltage is applied while being switched between the on-voltage and the off-voltage so as to apply the on-voltage for a set relatively long on-time.
  • the control means 22 sends a trigger signal to the scan driving means 15 so as to switch the pulse width of the on-voltage, that is, the on-time, when the charge remaining in each radiation detection element 7 reaches a predetermined charge amount. It comes to send.
  • the scan driving means 15 Upon receiving the trigger signal, the scan driving means 15 has a pulse width so as to shorten the pulse width of the ON voltage applied to each of the lines L1 to Lx of the scan line 5 from the gate driver 15b to a predetermined pulse width set in advance. Modulation is performed, and as shown in FIG. 11, the reset process Rm for one surface is continuously performed in a state where the ON time is shortened.
  • FIG. 11 and FIGS. 13 and 14 to be described later show a case where the on-time is shortened to 1 ⁇ 2 of the original on-time.
  • the present invention is not limited to this, and the on-time shortening rate is appropriately set. Is set to the value of
  • each radiation detection element 7 connected to the line Ln of the scanning line 5 via each TFT 8 will be described as an example.
  • each radiation detection element 7 When the radiation image capturing apparatus 1 is activated or transitions to a wakeful state, extra charges may remain in each radiation detection element 7 in some cases. Further, as described above, in each radiation detection element 7, dark charges are always generated due to thermal excitation caused by heat of the radiation detection element 7 itself.
  • control means 22 of the radiographic image capturing apparatus 1 is similar to the conventional case shown in FIG. 19 at the initial stage when the reset processing of each radiation detection element 7 is started as described above.
  • the ON time for applying the ON voltage to each of the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving means 15 is set to be a relatively long time interval.
  • the charge amount Q of the charge remaining in each radiation detection element 7 decreases as the on-voltage is applied for a relatively long on-time as described above, but as shown in FIG.
  • the charge remaining in each radiation detection element 7 reaches a predetermined charge amount Qa after the extra charge is released from the radiation detection element 7, each radiation detection element 7 can be obtained even if the reset process Rm for one surface is repeated. It has been found by the present inventors that the electric charge remaining in the inner surface does not fall below the electric charge amount Qa.
  • the number of reset processes Rm for one surface until the charge remaining in each radiation detection element 7 reaches a state where the charge amount Qa does not fall below the charge amount Qa (hereinafter referred to as a steady state) is originally the radiation image. It depends on the amount of extra charge remaining in each radiation detection element 7 when the imaging device 1 is activated or transitions to a wake-up state. It is necessary to perform a lot of reset processing Rm.
  • a state in which the maximum extra charge that can exist in each radiation detection element 7 at the time when resetting of each radiation detection element 7 is started is set, and from this state, The number of times of reset processing Rm for one surface required until the extra charge is released from the radiation detection element 7 to reach a steady state and the elapsed time required for the reset processing of each radiation detection element 7 are obtained in advance by experiments or the like. For example, it is stored in a memory of a CPU constituting the control means 22 of the radiographic image capturing apparatus 1 or a memory provided in the FPGA.
  • the control means 22 refers to the information on the number of times and the elapsed time stored in the memory or the like, starts reset processing of each radiation detection element 7, and then sets the number of times set in advance as described above.
  • the reset processing Rm for the surface is completed or when a preset elapsed time has elapsed, the charge remaining in each of the radiation detection elements 7 becomes a predetermined charge amount Qa.
  • the reset process Rm for one surface repeatedly performed thereafter is performed in a state in which the on-time is shortened.
  • the ON time is relatively long at the initial stage when the reset processing of each radiation detection element 7 is started, the charge amount Q of the charge remaining in each radiation detection element 7 is ON as shown in FIG.
  • the voltage decreases each time a voltage is applied, the reset process Rm for one surface is performed in a state where the on-time is shortened after the charge remaining in each radiation detection element 7 reaches a predetermined charge amount Qa. Even if is repeated, a steady state is maintained in which the charge remaining in each radiation detection element 7 does not drop below the charge amount Qa.
  • each radiation detection element 7 If the amount of extra charge remaining in each radiation detection element 7 is not so large at the time when resetting of each radiation detection element 7 is started, each radiation detection is performed before reaching the above time. Needless to say, the charge remaining in the element 7 may become a predetermined charge amount Qa.
  • the control means 22 of the radiographic image capturing apparatus 1 performs the stage where the charge remaining in each radiation detection element 7 reaches the predetermined charge amount Qa in this way, that is, for a predetermined number of times.
  • a ready signal is transmitted to the radiation generator 55 via the communication means such as the antenna device 39 or the base station 54. It is like that.
  • the radiographic imaging apparatus 1 is turned on even after a ready signal is transmitted when the charge remaining in each radiation detection element 7 reaches a predetermined charge amount Qa.
  • the reset process Rm for one surface is repeatedly performed with the time reduced.
  • the radiation generator 55 When the radiation generator 55 (see FIG. 9) receives the ready signal, it transmits it to the console 57, and upon receiving the ready signal, the console 57 displays the characters “READY” on the display unit. ing.
  • the radiation generator 55 puts the radiation source 52 into a standby state, for example, by starting rotation of the anode of the X-ray tube of the radiation source 52.
  • the irradiation start signal is sent from the exposure switch 56 to the radiation generator 55 via the console 57. Is sent.
  • the radiation generation device 55 receives the irradiation start signal from the exposure switch 56, the radiation generation device 55 transmits the irradiation start signal to the radiographic imaging device 1 via the base station 54 by a wireless method or a wired method. It is like that.
  • the control means 22 of the radiographic imaging apparatus 1 receives the irradiation start signal from the base station 54 via the communication means such as the antenna device 39, the on-time performed at that time is shortened as shown in FIG.
  • the reset process Rm for one surface is completed, the off-voltage is applied to all the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving means 15 to turn off the respective TFTs 8, and radiation Is transferred to a charge accumulation state in which the charges generated in each radiation detection element 7 are accumulated in each radiation detection element 7, and an interlock release signal is transmitted via communication means such as the antenna device 39.
  • the radiation generation device 55 receives the interlock release signal transmitted from the radiation image capturing device 1 via the communication means such as the antenna device 39 or the base station 54, the radiation source 52.
  • the X-ray tube is irradiated with radiation.
  • the time required for the reset process Rm for one surface is shorter than the time required for the conventional reset process Rm for one surface (see FIG. 19).
  • the radiation generator 55 is used at the same timing after the reset process Rm for one surface is started. Even if the irradiation start signal is transmitted from this time, in the present embodiment, since the time required for the reset process Rm for one surface is shortened, the time required until the reset process Rm for this one surface is completed is conventional. It becomes shorter than the case of.
  • the reset process Rm for one surface which is performed at the timing when the irradiation start signal is transmitted from the radiation generation device 55, is completed more quickly, and the radiation generation device 55 is more promptly processed.
  • An interlock release signal is transmitted. Therefore, the waiting time T until the radiation is actually emitted from the radiation generating apparatus after the operator fully presses and presses down the exposure switch 56 is compared with the waiting time T in the conventional case (see FIG. 20). Can be shortened.
  • FIG. 14 shows a case where an irradiation start signal is transmitted during the reset process Rm for the first surface whose on-time is shortened.
  • the on-time is shortened.
  • the irradiation start signal is transmitted after the reset process Rm for one surface is repeated.
  • the waiting time T is shortened also in that case.
  • each line L1 to L1 of the scanning line 5 in the reset process Rm for one surface that is repeatedly performed is performed. Since the ON time for Lx is shortened when the charge remaining in each radiation detection element 7 reaches the predetermined charge amount Qa, it is possible to promptly release the interlock release signal after receiving the irradiation start signal It becomes.
  • the radiographic image capturing apparatus 1 after the operator presses the exposure switch 56, the radiographic image capturing apparatus 1 promptly transmits an interlock release signal, and the radiation generating apparatus Radiation can be promptly emitted from 55 radiation sources 52.
  • the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 are easy to use for the operator.
  • the charge remaining in each radiation detection element 7 is predetermined. Until the charge amount Qa is reached, the ON time in the reset process Rm for one surface that is repeatedly performed is not shortened, but is controlled to have a relatively long time interval.
  • the power switch 36 of the radiographic image capturing apparatus 1 is pressed, the radiographic image capturing apparatus 1 is changed to an awake state, or reset processing of each radiation detection element 7 is started from the console 58.
  • the operator presses the exposure switch 56 halfway, and from the exposure switch 56, the reset process of each radiation detection element 7 is started.
  • the activation signal is transmitted to the radiation generation device 55, the activation signal is transmitted from the radiation generation device 55 to the radiation image capturing device 1, and the radiation image capturing device 1 resets each radiation detection element 7 using the activation signal as a trigger. It is also possible to configure to start.
  • the reset process for the next one surface is performed immediately after the voltage applied to the final line Lx of the scanning line 5 is switched from the on voltage to the off voltage in the reset processing Rm for one surface.
  • the case where the voltage applied to the first line L1 of the scanning line 5 is switched from the OFF voltage to the ON voltage has been described, but after the reset process Rm for one surface is completed, the next one surface is processed. It is also possible to configure so as to leave an interval of a predetermined time before starting the reset process Rm.
  • each radiation detection element is accurately reset, and after receiving the irradiation start signal.
  • the configurations of the radiographic image capturing apparatus and the radiographic image capturing system according to the present embodiment are the configurations of the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to the first embodiment described with reference to FIGS. Since it is the same as that of FIG. In the following, each means will be described with the same reference numerals as those in the first embodiment, but the radiographic image capturing apparatus 100 and the radiographic image capturing system itself will be described with respect to the radiographic image capturing apparatus and the radiographic image capturing system itself.
  • the imaging system 150 will be described.
  • control unit 22 of the radiographic image capturing apparatus 100 sequentially switches the scanning lines 5 for switching the voltage applied from the gate driver 15b of the scanning driving unit 15 between the on-voltage and the off-voltage so as to correspond to one surface.
  • the reset processing of each radiation detection element 7 is performed while repeatedly performing the reset processing Rm. This is the same as in the first embodiment.
  • the control unit 22 performs the reset processing for each radiation detection element 7 when the interval i is not provided between the reset processes Rm for one surface.
  • the reset process Rm for one surface is performed in the subsequent reset process. Is configured so that an interval i of a predetermined time is provided between the end of the process and the start of the reset process Rm for the next one surface.
  • the control means 22 When an interval i of a predetermined time is already provided before the stage in which the charge remaining in each radiation detection element 7 reaches a predetermined charge amount Qa, the control means 22 The predetermined time of interval i from the end of the reset process Rm for one face to the start of the reset process Rm for the next face at the stage where the charge remaining in the battery reaches a predetermined charge amount Qa Configured to extend.
  • each radiation detection element 7 from the state in which the maximum extra charge that may exist in each radiation detection element 7 remains at the time when the reset processing of each radiation detection element 7 is started, this excess from each radiation detection element 7.
  • the number of times of resetting process Rm for one surface necessary until the above-described steady state is released and the elapsed time required for resetting of each radiation detecting element 7 depends on the control means 22 of the radiographic imaging apparatus 100. It is stored in advance in a memory of a CPU or a memory provided in the FPGA.
  • the control means 22 refers to the information on the number of times and the elapsed time stored in the memory or the like, starts reset processing of each radiation detection element 7, and then sets the number of times set in advance as described above.
  • the reset process Rm for the surface is completed, or when a preset elapsed time has elapsed, and when the charge remaining in each of the radiation detection elements 7 reaches a predetermined charge amount Qa, As shown in FIGS. 15 and 16, an interval i of a predetermined time is provided between the reset process Rm for one surface and the reset process Rm for the next surface.
  • the reset process Rm for one surface is completed, the reset process Rm for each radiation detection element 7 is changed so that the reset process Rm for the next one surface is performed after a predetermined time interval i. It is supposed to be.
  • the ON time in the reset process Rm for one surface is not shortened.
  • the predetermined time of the newly provided interval i, the extension rate of the predetermined time of the already provided interval i, etc. are set suitably.
  • the control means 22 sends all of the scanning lines 5 from the gate driver 15 b of the scanning drive means 15.
  • Each of the TFTs 8 serving as switching means is turned off by applying an off voltage to the lines L1 to Lx, and each radiation detecting element 7 is shifted to the charge accumulation state, and interlocked via communication means such as the antenna device 39. A release signal is transmitted.
  • an operator such as a radiographer can switch the exposure switch 56 during a newly provided interval i or during an interval i in which a predetermined time is extended.
  • the radiographic imaging device 100 side does not perform the reset process Rm for one surface, so immediately after receiving the irradiation start signal. It is possible to transmit an interlock release signal to the radiation generator 55 via a communication unit such as the antenna device 39.
  • the waiting time T until the radiation is actually emitted from the radiation source 52 of the radiation generating device 55 after the operator fully depresses and presses the exposure switch 56 is very high as shown in FIG. Shorter.
  • the off voltage is applied to all the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving means 15, so that the control means 22 Subsequently, the state in which the off voltage is applied to all the lines L1 to Lx of the scanning line 5 is maintained, and each radiation detection element 7 is subsequently shifted to the charge accumulation state.
  • the length of each ON time in each of the lines L1 to Lx of the scanning line 5 is the ON time before the ON time in FIG. Although it is described so as to be shorter than the on-time in the conventional case shown in FIG. 19, this does not mean that the on-time is shortened in the case of FIG. 15, and is set to the same on-time. As in the case of FIG. 11 and FIG. 19, it is set to an appropriate length.
  • the time required for the reset process Rm for one surface is equal to the reset process Rm for one surface before the ON time is shortened in FIG. Although described so as to be shorter than the time required for the reset processing Rm for one surface, this does not mean that the time required for the reset processing Rm for one surface is shortened in the case of FIG.
  • FIG. 16 shows a case where the irradiation start signal is transmitted during the interval i after the reset process Rm for the first surface is completed after the interval i is provided.
  • the irradiation start signal is transmitted after the reset process Rm and the interval i for one surface are repeated.
  • the waiting time T becomes very short.
  • the interval i is not provided between the reset processes Rm for one surface.
  • the reset process Rm for one surface is completed in the subsequent reset processing, and then the next one surface.
  • Interval i for a predetermined time is provided until the reset process Rm is started.
  • the predetermined time of the interval i is set at a stage where the charge remaining in each radiation detection element 7 reaches a predetermined charge amount Qa. Configured to extend.
  • the interlock release signal can be promptly transmitted after the irradiation start signal is received.
  • an interlock release signal is promptly transmitted from the radiographic image capturing apparatus 100 in this way, and the radiation generating apparatus It becomes possible to irradiate radiation from 55 radiation sources 52 promptly.
  • the radiographic image capturing apparatus 100 and the radiographic image capturing system 150 according to the embodiment are easy to use for the operator.
  • the ON time in the reset process Rm for one surface that is repeatedly performed is not shortened, and becomes a relatively long time interval. To be controlled.
  • the configurations of the radiographic image capturing apparatus and the radiographic image capturing system according to the present embodiment are the configurations of the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to the first embodiment described with reference to FIGS. Since it is the same as that of FIG.
  • each means will be described with the same reference numerals as those in the first and second embodiments described above, but the radiographic image capturing apparatus and the radiographic image capturing system itself will be described.
  • the radiation image capturing system 250 will be described.
  • control unit 22 of the radiographic image capturing apparatus 200 sequentially switches the scanning line 5 for switching the voltage applied from the gate driver 15b of the scanning driving unit 15 between the on-voltage and the off-voltage so as to correspond to one surface.
  • the reset processing of each radiation detection element 7 is performed while repeatedly performing the reset processing Rm. This is the same as the first and second embodiments.
  • the control means 22 is in a stage where the charge remaining in each radiation detection element becomes a predetermined charge amount Qa during the reset process of each radiation detection element 7.
  • the reset processing Rm for one surface is performed by shortening the ON time in the reset processing Rm for one surface that is repeatedly performed. This is the same as in the first embodiment.
  • control means 22 shortens the ON time as described above, and at the stage where the charge remaining in each radiation detection element reaches a predetermined charge amount Qa as shown in FIG. 17 and FIG.
  • the interval i is not provided between the reset processes Rm for the surfaces, the interval i for a predetermined time is provided between the reset processes Rm for one surface, and the reset processing after the above-described stage is performed.
  • the control means 22 extends the predetermined time of the interval i between the reset processes Rm for one surface. Thus, the reset process after the above-described stage is performed. These are the same as in the second embodiment.
  • the number of reset processes Rm for one surface described above and the elapsed time required for the reset process of each radiation detection element 7 are stored in advance in a memory or the like, and the control means 22 stores these information. Configured to refer.
  • each radiation detection element 7 by repeatedly performing the reset process Rm for one surface whose ON time is shortened and the interval i for a predetermined time, the communication of the antenna device 39 and the like is performed.
  • the control means 22 applies the off voltage to all the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving means 15 to turn off each TFT 8 which is the switching means.
  • Each radiation detection element 7 is shifted to a charge accumulation state by being put in a state, and an interlock release signal is transmitted via communication means such as the antenna device 39.
  • an operator such as a radiographer sets the exposure switch 56 during a newly provided interval i or during an interval i in which a predetermined time is extended.
  • the irradiation start signal is transmitted from the radiation generating device 55 by pressing it all the way down, on the radiation image capturing device 200 side, all the lines of the scanning line 5 from the gate driver 15b of the scanning driving means 15 as shown in FIG. Since the off voltage is applied to L1 to Lx, the control means 22 maintains the state in which the off voltage is applied to all the lines L1 to Lx of the scanning line 5 as it is, and each radiation detection element 7 is charged. And an interlock release signal is promptly transmitted to the radiation generating device 55 through communication means such as the antenna device 39.
  • the reset process Rm for one surface which is performed at the timing when the irradiation start signal is transmitted from the radiation generation device 55, is completed more quickly, and the interlock release signal is transmitted to the radiation generation device 55 more quickly. Therefore, the waiting time T until the radiation is actually emitted from the radiation generating apparatus after the operator fully presses and presses the exposure switch 56 is shorter than the waiting time T in the conventional case. It becomes possible to do. This is the same as in the case of the first embodiment described above.
  • the waiting time T can be made shorter than in the conventional case.
  • the time required for the reset process Rm for one surface before the on-time is shortened is one surface before the on-time in FIG. 14 is shortened.
  • the reset process Rm and the time required for the reset process Rm for one surface in the case shown in FIG. 20 are described as being shorter than the time required for the reset process Rm in the case of FIG. 17 and FIG. In addition, it does not mean shortening the time required for the reset process Rm for one surface before the ON time is shortened, and is set to an appropriate length.
  • the effects of the first embodiment and the second embodiment are effectively exhibited, and the radiographic image is displayed.
  • the imaging apparatus 200 can promptly transmit an interlock release signal after receiving the irradiation start signal. Further, in the radiographic imaging system 250, after the operator depresses the exposure switch 56, an interlock release signal is promptly transmitted from the radiographic imaging apparatus 200, and radiation is promptly transmitted from the radiation source 52 of the radiation generating apparatus 55. Irradiation is possible.
  • the waiting time T from when the operator such as a radiologist presses the exposure switch 56 until the interlock is released and radiation is actually started is very short, which is convenient for the operator. It will be a thing.
  • the reset process for one surface is repeatedly performed until the charge remaining in each radiation detection element 7 reaches a predetermined charge amount Qa after the start of the reset process of each radiation detection element 7. Since the ON time in Rm is not shortened and is controlled so as to have a relatively long time interval, each radiation detection element 7 is sufficiently discharged with an excessive charge remaining inside, and each radiation detection element It is possible to accurately perform the reset process, and it is possible to accurately prevent the deterioration of the image quality of the radiation image.
  • the operator presses the exposure switch 56 halfway, and an activation signal is transmitted from the exposure switch 56 to the radiation generator 55.
  • the activation signal is transmitted from the radiation generation device 55 to the radiation image capturing device 100, and the reset processing of each radiation detection element 7 is started in the radiation image capturing device 100 using the start signal as a trigger.
  • a ready signal is transmitted from the control means 22 to the radiation generator 55, or a ready signal is transmitted.

Landscapes

  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Multimedia (AREA)
  • Signal Processing (AREA)
  • Radiology & Medical Imaging (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
  • Pathology (AREA)
  • Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Transforming Light Signals Into Electric Signals (AREA)
  • Measurement Of Radiation (AREA)

Abstract

La présente invention se rapporte à un dispositif de prise d'images radiographiques qui effectue de façon appropriée des processus de réinitialisation de chaque élément détecteur de rayonnement respectif et qui peut également transmettre rapidement des signaux pour libérer l'interverrouillage lors de la réception de signaux de début d'éclairage. Lors de la commutation séquentielle de lignes de balayage (5) qui sont commutées entre une tension de fonctionnement et une tension de coupure d'une tension qui est appliquée par un dispositif de commande de grille (15b) d'un moyen d'entraînement de balayage (15) et lors de la réalisation d'un processus de réinitialisation de chaque élément de détection de rayonnement respectif (7) tout en répétant un processus de réinitialisation d'un écran (Rm), un dispositif de prise d'images radiographiques (1) écourte le temps de fonctionnement et effectue le processus de réinitialisation d'un écran (Rm) à l'étape au cours de laquelle une charge électrique qui reste dans chaque élément de détection de rayonnement respectif (7) atteint une quantité de charge prescrite (Qa). Lors de la réception d'un signal de début d'éclairage par l'intermédiaire d'un moyen de communication (39), le dispositif de prise d'images radiographiques applique les tensions de coupure depuis le dispositif de commande de grille (15b) à toutes les lignes de balayage (5), met chaque moyen de commutation respectif (8) à l'état d'arrêt et transmet un signal pour libérer l'interverrouillage par l'intermédiaire du moyen de communication (39) à la fin du processus de réinitialisation d'un écran (Rm) au cours duquel le temps de fonctionnement est écourté.
PCT/JP2010/073136 2010-01-27 2010-12-22 Dispositif de prise d'images radiographiques et système de prise d'images radiographiques WO2011092981A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP2011551712A JP5621788B2 (ja) 2010-01-27 2010-12-22 放射線画像撮影装置および放射線画像撮影システム

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2010014913 2010-01-27
JP2010-014913 2010-01-27

Publications (1)

Publication Number Publication Date
WO2011092981A1 true WO2011092981A1 (fr) 2011-08-04

Family

ID=44318980

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2010/073136 WO2011092981A1 (fr) 2010-01-27 2010-12-22 Dispositif de prise d'images radiographiques et système de prise d'images radiographiques

Country Status (2)

Country Link
JP (1) JP5621788B2 (fr)
WO (1) WO2011092981A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013125111A1 (fr) * 2012-02-22 2013-08-29 富士フイルム株式会社 Dispositif de commande d'imagerie de radiographie, système d'imagerie de radiographie, procédé de commande de dispositif d'imagerie de radiographie et programme de commande d'imagerie de radiographie
JP2016500019A (ja) * 2012-11-15 2016-01-07 ジュン シン，ドン Ｘ線システムのためのデジタル医療映像システム及び装置

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH11151233A (ja) * 1997-11-20 1999-06-08 Canon Inc 放射線撮像装置及び撮像方法
JP2003033340A (ja) * 2001-07-19 2003-02-04 Canon Inc Ｘ線撮影システム及びその制御方法並びにプログラムコード、記憶媒体
JP2009233039A (ja) * 2008-03-26 2009-10-15 Fujifilm Corp 放射線画像検出装置

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH11151233A (ja) * 1997-11-20 1999-06-08 Canon Inc 放射線撮像装置及び撮像方法
JP2003033340A (ja) * 2001-07-19 2003-02-04 Canon Inc Ｘ線撮影システム及びその制御方法並びにプログラムコード、記憶媒体
JP2009233039A (ja) * 2008-03-26 2009-10-15 Fujifilm Corp 放射線画像検出装置

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013125111A1 (fr) * 2012-02-22 2013-08-29 富士フイルム株式会社 Dispositif de commande d'imagerie de radiographie, système d'imagerie de radiographie, procédé de commande de dispositif d'imagerie de radiographie et programme de commande d'imagerie de radiographie
JP2016500019A (ja) * 2012-11-15 2016-01-07 ジュン シン，ドン Ｘ線システムのためのデジタル医療映像システム及び装置

Also Published As

Publication number Publication date
JP5621788B2 (ja) 2014-11-12
JPWO2011092981A1 (ja) 2013-05-30

Similar Documents

Publication Publication Date Title
JP5866814B2 (ja) 放射線画像撮影システムおよび放射線画像撮影装置
JP2010264085A (ja) 放射線画像撮影装置
JP2011193306A (ja) 放射線画像撮影装置および放射線画像撮影システム
JP2010121944A (ja) 可搬型放射線画像撮影装置および放射線画像撮影システム
JP2010253089A (ja) 放射線画像生成装置及び放射線画像生成システム
JP2010264181A (ja) 放射線画像撮影装置
JP5648404B2 (ja) 放射線画像撮影システムおよび放射線画像撮影装置
JP2011172606A (ja) 放射線画像撮影装置および放射線画像撮影システム
JP5396814B2 (ja) 放射線画像撮影システム
JP5332619B2 (ja) 可搬型放射線画像撮影装置および放射線画像撮影システム
JP2010212925A (ja) 可搬型放射線画像撮影装置および放射線画像撮影システム
JP2013078410A (ja) 放射線画像撮影システムおよび放射線画像撮影装置
JP5621788B2 (ja) 放射線画像撮影装置および放射線画像撮影システム
JP5099000B2 (ja) 可搬型放射線画像撮影装置および放射線画像撮影システム
JP2011133302A (ja) 放射線画像撮影装置および放射線画像撮影システム
WO2010073838A1 (fr) Appareil de capture d'image radiologique portable et système de capture d'image radiologique
JP2011130880A (ja) 放射線画像撮影装置および放射線画像撮影システム
JP2011153876A (ja) 放射線画像撮影装置および放射線画像撮影システム
JP5672244B2 (ja) 放射線画像撮影装置および放射線画像撮影システム
JP5626225B2 (ja) 放射線画像撮影装置および放射線画像撮影システム
JP2006122121A (ja) 放射線画像撮影システム
JP2012016464A (ja) 放射線画像撮影装置および放射線画像撮影システム
US10973490B2 (en) Radiation image photographing apparatus and radiation image photographing system for radiation image photographing process and dark image acquiring process
JP2013022044A (ja) 放射線画像撮影システムおよび放射線画像撮影装置
JP2011156241A (ja) 放射線画像撮影装置および放射線画像撮影システム

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 10844735

Country of ref document: EP

Kind code of ref document: A1

WWE Wipo information: entry into national phase

Ref document number: 2011551712

Country of ref document: JP

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 10844735

Country of ref document: EP

Kind code of ref document: A1