JP5099000B2 - Portable radiographic imaging device and radiographic imaging system - Google Patents

Description

  The present invention relates to a portable radiographic image capturing apparatus and a radiographic image capturing system, and more particularly to a portable radiographic image capturing apparatus that performs a reset process of a radiation detecting element that discharges an excess charge accumulated in the radiation detecting element. The present invention relates to a radiographic image capturing system using a computer.

  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. In the present invention, 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 conventionally been formed integrally with a support base (or a bucky device) (see, for example, Patent Document 1). However, in recent years, a portable radiographic image capturing apparatus in which a radiation detection element or the like is accommodated in a housing has been developed and put into practical use (see, for example, Patent Documents 2 and 3). In these portable radiographic imaging apparatuses, a battery is built in.

  By the way, the internal structure of the portable radiographic image capturing apparatus generally has a plurality of scanning lines 5 and a plurality of signals arranged on the substrate 4 so as to cross each other, as shown in FIGS. A plurality of radiation detection elements 7 are two-dimensionally (matrix-like) arranged in each small region r partitioned by the line 6. As described above, the radiation detection element 7 generates charges in accordance with the dose of the irradiated radiation, the charges of each radiation detection element 7 are read out, and are converted into charge voltages by the readout circuit 17. It is extracted as image data after being amplified.

  However, even when no radiation is applied to the portable radiographic imaging device, charges are generated inside due to thermal excitation or the like due to heat of the radiation detection element 7 itself, and the charge is a so-called dark charge. Accumulated within. Then, when radiographic imaging is performed in a state where a large amount of this dark charge exists in each radiation detection element 7, when the above-described charges generated by radiation irradiation are read out as image data from each radiation detection element 7, This large amount of dark charge is read out together and a large noise component is superimposed on the image data.

  In order to remove the noise component due to this dark charge as much as possible, at the time of radiographic image capturing, dark charges accumulated in the radiation detecting element 7 or the like usually immediately before the radiation image capturing apparatus is irradiated with radiation, etc. A reset process is performed to remove the excess charge. Further, the reset process of the radiation detection element 7 is appropriately performed not only at the time of radiographic image capturing as described above but also as necessary.

  In the reset process of the radiation detection element 7, as shown in FIG. 3, FIG. 4, etc., the gate electrode 8g of the TFT 8 (Thin Film Transistor) which is the switch means of each radiation detection element 7 connected to each scanning line 5 is applied. An on-voltage is applied via the scanning line 5 to open the gate of the TFT 8, and extra charge accumulated in the radiation detection element 7 is discharged to the signal line 6 via the TFT 8 to perform reset processing.

  At that time, as described in Patent Document 4, for example, the scanning line 5 to which the ON voltage is applied is set for each of the lines L1 to Lx (see FIG. 7 to be described later) or for each of a plurality of (for example, three) lines. It is possible to sequentially discharge excess charges accumulated from the radiation detection elements 7 while sequentially switching. However, since several thousand to several tens of thousands of scanning lines 5 are usually arranged in the radiographic image capturing apparatus, the on-voltage is applied to each scanning line in this way. A relatively long time is required for the reset process.

  Further, in such a case, in order to shorten the time required for the reset process of the radiation detection element 7, if the time for applying the ON voltage to each line L <b> 1 to Lx of the scanning line 5 is shortened, the darkness from each radiation detection element 7 is reduced. The TFT 8 is turned off before the extra charge such as the electric charge is completely discharged, and the extra charge cannot be sufficiently removed from each radiation detection element 7.

Therefore, as described in Patent Document 4, on-voltages are simultaneously applied to the lines L1 to Lx of the scanning line 5 so that all TFTs 8 are simultaneously turned on and accumulated from the radiation detecting elements 7 simultaneously. It can be configured to release excess charge. With this configuration, it is possible to reduce the time required for resetting all the radiation detection elements 7 while securing the time for sufficiently removing excess charges from each radiation detection element 7.
JP-A-9-73144 JP 2006-058124 A JP-A-6-342099 JP-A-9-131337

  By the way, the TFT 8 as the switch means described above is connected to one electrode (the first electrode 74 shown in FIG. 7 and the like) of the radiation detection element 7, and the electrons accumulated in the radiation detection element 7 during the reset process. -One charge out of the holes flows out to the signal line 6 through the TFT 8. In addition, a bias line 9 for applying a bias voltage to the radiation detection element 7 is connected to the other electrode (second electrode 78 shown in FIG. 7 and the like) of the radiation detection element 7. It is bound to the connection 10 and connected to the bias power supply 14. In the reset process, the other charge of electrons and holes accumulated in the radiation detection element 7 flows out to the bias line 9, collects in the connection line 10, and flows into the bias power source 14.

  In that case, a relatively large amount of electrons are applied to each radiation detection element 7 particularly in the first reset process performed after power is supplied to each radiation detection element 7 such as after turning on the power of the radiation imaging apparatus. In some cases, holes are accumulated. In such a case, if the on-voltage is simultaneously applied to all the scanning lines 5 and reset processing is performed as described above, the charges accumulated in the bias lines 9 flow out from the radiation detection elements 7, and the bias lines 9 A large amount of current flows due to the collection of charges in the connection 10.

  If the radiographic imaging apparatus is used for many years and a large amount of charge flows out to the bias line 9 or the connection 10 repeatedly, the disconnection may occur particularly in the connection 10 part. Is disconnected, an appropriate bias voltage is not applied to each radiation detection element 7, and excess charge does not flow out from the electrode of each radiation detection element 7 (electrode 78 shown in FIG. 7 etc.). The irradiated radiation cannot be accurately detected.

  In a conventional radiographic imaging device (FPD) integrally formed with a support base or a Bucky device, power is always supplied to the FPD through the support base and the like, so it is possible to perform reset processing frequently. It is possible to prevent disconnection of the connection line 10 and the like by releasing the charge before the large charge is stored in each radiation detection element 7 and reducing the amount of current flowing through the bias line 9 and the connection line 10.

  However, in a portable radiographic imaging apparatus with a built-in battery, if the reset process is performed frequently in the same manner, the amount of battery power consumed in the reset process increases and the battery is consumed. . Therefore, in the portable radiographic imaging apparatus, it is necessary to configure the radiation detection element 7 to be reset only when necessary, such as before radiographic imaging. Thus, the possibility of disconnection of the connection 10 or the like occurs.

  Therefore, in the portable radiographic imaging device, it is required that the radiation detection element 7 is reset so that the bias line 9 and the connection 10 are not disconnected while preventing the battery from being consumed. In addition, in the reset process of the radiation detection elements 7, it is required that extra charges can be reliably removed from each radiation detection element 7.

  The present invention has been made in view of the above-described problems. Portable radiographic imaging capable of preventing battery consumption and disconnection of a bias line and the like and sufficiently removing excess charges from a radiation detection element. An object is to provide an apparatus and a radiographic imaging system.

In order to solve the above problem, the portable radiographic imaging device of the present invention is:
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; A detector comprising:
A bias line connected to each of the radiation detection elements;
A bias power source for applying a bias voltage to each radiation detection element via the bias line;
When an on-voltage is applied to the scanning line arranged and connected to each radiation detection element, a charge generated in the radiation detection element is released, and an off-voltage is applied to the connected scanning line. Switch means for accumulating charges generated in the radiation detection element in the radiation detection element;
A scanning drive unit that includes a power supply circuit and a gate driver, and controls a voltage applied to the switch unit via each scanning line;
With
A battery for supplying power to each of the above means is incorporated,
The scanning drive unit controls a voltage applied to the switch unit via each scanning line during a reset process of the radiation detection element that discharges excess charges accumulated in the radiation detection element. The current flowing out from the radiation detecting elements to the bias line is limited.

Moreover, the radiographic imaging system of the present invention is
A portable radiographic imaging device of the present invention comprising a communication means capable of communicating with the outside;
A radiation generator comprising: a radiation source that irradiates radiation to the portable radiation imaging apparatus; and an operation console that activates the radiation source and includes an irradiation start switch that instructs the radiation source to start radiation irradiation; ,
With
When the scanning drive unit of the portable radiographic image capturing apparatus receives the radiation source activation signal transmitted from the console via the communication unit, it starts resetting the radiation detection element. Features.

  According to the portable radiographic image capturing apparatus and the radiographic image capturing system of the system of the present invention, on voltages with different voltage values are applied stepwise, an on voltage with a short pulse width is applied multiple times, etc. Then, by controlling the voltage applied to the switch means (TFT) through each scanning line, as shown in FIG. 12B and FIG. The amount of current that flows through the bias line and connection is limited compared to when the normal on-voltage is applied to each switch means from the beginning during reset processing (see the dashed line in each figure). Becomes lower.

  Therefore, the reset process of the radiation detection element is repeated, and it is possible to surely reduce the probability that a large amount of current flows through the bias line and the connection and the connection is disconnected. Can be prevented. In addition, since it is not necessary to repeat the reset process of the radiation detection element more frequently than necessary, it is possible to prevent the battery power consumption by accurately preventing the power consumption of the battery from increasing by repeating the reset process. It becomes.

  Furthermore, for example, if all the switch elements are turned on at the same time and each radiation detection element is reset at the same time, all radiation detection can be performed while ensuring sufficient time to remove excess charges from each radiation detection element. It is possible to shorten the time required for the element reset processing.

  Embodiments of a portable radiographic imaging device and a radiographic imaging system according to the present invention will be described below with reference to the drawings.

  Hereinafter, the portable radiographic imaging device is simply referred to as a radiographic imaging device. A so-called indirect radiation image capturing apparatus that includes a scintillator or the like and converts irradiated radiation into electromagnetic waves of other wavelengths such as visible light to obtain an electric signal will be described below. Can also be applied to a direct radiographic imaging apparatus.

[Radiation imaging equipment]
[First Embodiment]
FIG. 1 is an external perspective view of the radiographic image capturing apparatus according to the present embodiment, and FIG. 2 is a cross-sectional view taken along line AA in FIG. As shown in FIGS. 1 and 2, the radiographic imaging apparatus 1 according to the present embodiment is configured as a portable (cassette type) apparatus in which a scintillator 3, a substrate 4, and the like are housed in a housing 2. .

  The housing 2 is formed of a material such as a carbon plate or plastic that transmits radiation at least on a surface R (hereinafter referred to as a radiation incident surface R) that receives radiation. 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.

  As shown in FIG. 1, 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. In the present embodiment, an antenna device 39 that is a communication unit for wirelessly communicating with the outside is embedded in the side surface of the lid member 38.

  As shown in FIG. 2, a base 31 is disposed inside the housing 2 via a thin lead plate or the like (not shown) on the lower side of the substrate 4. The disposed PCB substrate 33, the buffer member 34, and the like are attached. In the present embodiment, 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 attached to a detection unit P, which will be described later, of the substrate 4. As the scintillator 3, for example, a scintillator 3 that has a phosphor as a main component and converts it into an electromagnetic wave having a wavelength of 300 to 800 nm, that is, an electromagnetic wave centered on visible light when it receives incident radiation, is used.

  In the present embodiment, 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.

  Thus, the entire region r in which a plurality of radiation detection elements 7 arranged in a two-dimensional manner are provided in each small region r partitioned by the scanning line 5 and the signal line 6, that is, shown by a one-dot chain line in FIG. The region is a detection unit P.

  In the present embodiment, 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 applied to the gate electrode 8g, and is generated and accumulated in the radiation detection element 7. The charged electric charge is discharged 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 accumulated in the radiation detection element 7.

  Here, the structure of the radiation detection element 7 and the TFT 8 in this embodiment will be briefly described with reference to the cross-sectional view shown in FIG. FIG. 5 is a sectional view taken along line XX 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). The first electrode 74 of the radiation detecting element 7 is connected to the upper portion of the gate electrode 8g on the gate insulating layer 81 made of SiN _x ) or the like via the 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 the electrodes 8s and 8d from above. In addition, 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.

  In the radiation detecting element 7, 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.

  On the first electrode 74, an n layer 75 formed in an n-type by doping a hydrogenated amorphous silicon with a group VI element, an i layer 76 which is a conversion layer formed of hydrogenated amorphous silicon, and a hydrogenated amorphous 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.

  When radiation enters from the radiation incident surface R of the housing 2 of the radiographic imaging apparatus 1 and is converted into an electromagnetic wave such as visible light by the scintillator 3, and the converted electromagnetic wave is irradiated from above in the figure, the electromagnetic wave is detected by radiation. The electron hole pair is generated in the i layer 76 by reaching the i layer 76 of the element 7. In this way, the radiation detection element 7 converts the electromagnetic waves irradiated from the scintillator 3 into electric charges.

  On the p layer 77, 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. In the present embodiment, 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.

  As shown in FIGS. 3 and 4, in this embodiment, 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. In addition, each bias line 9 is bound to one connection 10 at a position outside the detection portion P of the substrate 4.

  In this embodiment, as shown in FIG. 3, 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. As shown in FIG. 6, a COF (Chip On Film) 12 in which a chip such as an IC 12 a is incorporated in each input / output terminal 11 is an anisotropic conductive adhesive film (Anisotropic Conductive Film) or anisotropic conductive paste (Anisotropic paste). It is connected via an anisotropic conductive adhesive material 13 such as 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. Thus, the board | substrate 4 part of the radiographic imaging apparatus 1 is formed. In FIG. 6, illustration of the electronic component 32 and the like is omitted.

  Here, the circuit configuration of the radiation image capturing apparatus 1 will be described. FIG. 7 is an equivalent circuit diagram of the radiation image capturing apparatus 1 according to the present embodiment, and FIG. 8 is an equivalent circuit diagram of one pixel constituting the detection unit P.

  As described above, 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. In the present embodiment, the current detection means 43 for detecting the amount of current flowing through the connection 10 (bias line 9) is provided in the connection 10 of the bias line 9, which will be described later.

  In the present embodiment, as can be seen from the fact that the bias line 9 is connected to the p-layer 77 side (see FIG. 5) of the radiation detection element 7 via the second electrode 78, A voltage equal to or lower than the voltage applied to the first electrode 74 side of the radiation detection element 7 is applied to the second electrode 78 of the radiation detection element 7 as a bias voltage via the bias line 9.

  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 each 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.

  In this embodiment, the scanning drive unit 15 includes a power supply circuit 15a and a gate driver 15b, and controls a voltage applied to the gate electrode 8g of the TFT 8 via each scanning line 5 connected to the gate driver 15b. It is supposed to be.

  Specifically, the power supply circuit 15a of the scanning drive unit 15 sets the voltage values of the on voltage and the off voltage applied to each scanning line 5 from the gate driver 15b to predetermined voltage values, and supplies them to the gate driver 15b. It is supposed to be. Further, the gate driver 15b of the scanning driving means 15 can modulate the pulse width and duty ratio of the pulse wave of the on-voltage applied to each scanning line 5 by pulse width modulation (PWM).

  A method for applying the ON voltage to the TFT 8 via the scanning lines 5 from the scanning driving means 15 will be described in detail later.

  Each signal line 6 is connected to each readout circuit 17 formed in the readout IC 16. Note that a predetermined number of readout circuits 17 are provided in the readout IC 16, and by providing a plurality of readout ICs 16, readout circuits 17 corresponding to the number of signal lines 6 are provided.

  The readout circuit 17 includes an amplifier circuit 18, a correlated double sampling circuit 19, an analog multiplexer 21, and an A / D converter 20. 7 and 8, the correlated double sampling circuit 19 is represented as CDS. In FIG. 8, the analog multiplexer 21 is omitted.

In the present embodiment, 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. 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 initial voltage V ₀ is applied to the non-inverting input terminal on the input side of the amplifier circuit 18. ing. The initial voltage V ₀ is set to a suitable value.

  The charge reset switch 18c of the amplifier circuit 18 is connected to the control means 22 described later, and is controlled to be turned on / off by the control means 22. When the charge reset switch 18c is off and the TFT 8 of the radiation detection element 7 is turned on (that is, when an on-voltage is applied to the gate electrode 8g of the TFT 8 via the scanning line 5), the radiation The electric charge discharged from the detection element 7 flows into the capacitor 18b and is accumulated, and a voltage value corresponding to the accumulated electric charge is output from the output side of the operational amplifier 18a.

  In this way, the amplifier circuit 18 outputs a voltage value in accordance with the amount of charge output from each radiation detection element 7 to perform charge voltage conversion and amplify. 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. Note that 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. In this embodiment, 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.

  That is, in the correlated double sampling circuit 19, after the amplifier circuit 18 is reset, the charge reset switch 18c is turned off, and the charge discharged from the radiation detection element 7 starts to flow into the capacitor 18b and accumulate. When the first pulse signal is received from the control means 22 at that time, the voltage value output from the amplifier circuit 18 at that time is held.

  Then, after a lapse of a predetermined time from that point, when the second pulse signal is received from the control means 22 when the electric charge released from the radiation detecting element 7 flows into the capacitor 18b and is accumulated, it is amplified again at that point. The voltage value output from the circuit 18 is held, and the difference value between these voltage values is output downstream 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 and 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 is constituted by a computer in which a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), an input / output interface and the like (not shown) are connected to a bus. It may be configured by a dedicated control circuit. And the control means 22 controls operation | movement etc. of each member of the radiographic imaging apparatus 1. The control means 22 is connected to a storage means 40 composed of a DRAM (Dynamic RAM) or the like.

  The control unit 22 is connected to the antenna device 39 described above, and further supplies power to each member such as the detection unit P, the scanning drive unit 15, the readout circuit 17, the storage unit 40, and the bias power source 14. A battery 41 is connected. As described above, the battery 41 is built in the housing 2 of the radiographic imaging apparatus 1, and the battery 41 has a connection terminal 42 for supplying power from the external device to the battery 41 to charge the battery 41. It is attached.

  As described above, the 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.

  In addition, the control means 22 is configured such that a signal is input manually by an operator such as a radiologist operating the power switch 36 or wirelessly through an antenna device 39 from an external device. The power supply state to the member is set to a power saving mode (sleep mode) in which the supply of power to the radiation detecting element 7 or the like is stopped and power is supplied only to the necessary member, and the power is supplied to the radiation detecting element 7 or the like. Thus, it is configured to be able to switch between a radiographable mode (wake up mode) that enables radiographic imaging.

  In the power saving mode, since power is not supplied to the radiation detection element 7 and the like, power consumption of the battery 41 can be suppressed, but radiographic imaging cannot be performed. In the photographing enabled mode, power is supplied to each member such as the radiation detection element 7 and radiation detection is possible, but the power of the battery 41 is consumed. For this reason, the control unit 22 switches the power supply state to each member to the photographing enabled mode, and if the radiation image capturing apparatus 1 is not irradiated with radiation even after a predetermined time has elapsed, the power supply state to each member. Switch to the power saving mode.

  The current detection means 43 detects a current flowing in the connection 10 in which the bias lines 9 are bundled. In the present embodiment, the current detection unit 43 includes a resistor having a predetermined resistance value connected in series to the connection 10 and a differential amplifier that measures a voltage between both terminals of the resistor, although not illustrated. By measuring the voltage between both terminals of the resistor with a differential amplifier, the current flowing through the connection 10 is converted into a voltage value and detected.

  As the resistor provided in the current detecting means 43, a resistor having a relatively large resistance value is used in order to amplify a weak current flowing through each bias line 9 and connection 10 and convert it to a voltage value. The current detection means 43 outputs a voltage value corresponding to the detected current amount of the connection 10 to the control means 22.

  Note that, for example, when reading the electric charge accumulated in the radiation detection element 7 by radiation irradiation at the time of radiographic imaging, a current also flows through the bias line 9 and the connection 10, but the resistance value of the resistance of the current detection unit 43 is If it is relatively large, the current flowing through the bias line 9 and the connection line 10 will be hindered.

  For this reason, the current detecting means 43 is provided with a switch (not shown) for short-circuiting both terminals of the resistor, and the control means 22 is normally turned on to short-circuit between both terminals of the resistor. When the voltage value information corresponding to the amount of current flowing through the bias line 9 or the connection 10 is necessary, the switch is turned off, and the voltage corresponding to the current amount of the connection 10 detected from the current detection means 43 The value is output to the control means 22 and the scanning drive means 15.

  Next, the operation of the radiographic image capturing apparatus 1 according to the present embodiment will be described, and the application of the on-voltage to the TFTs 8 via the scanning lines 5 from the scanning drive unit 15 in the radiographic image capturing apparatus 1 according to the present embodiment will be described. How to let it be explained.

  The control means 22 (see FIG. 7) of the radiographic image capturing apparatus 1 receives radiation signals when an awakening signal is input manually by an operator to perform radiographic image capturing or wirelessly from an external device via the antenna device 39. The power supply state for each member of the image capturing apparatus 1 is switched from the power saving mode to the image capturing possible mode.

  The power supply circuit 15a of the scanning drive means 15 is used to close the off voltage Voff applied to the gate electrode 8g of the TFT 8 serving as the switch means of each radiation detection element 7 via the scanning line 5, that is, the TFT 8 of each radiation detection element 7. For example, as shown in FIG. 9, a voltage value of −10 [V] is applied as the OFF voltage Voff.

  The control means 22 transmits a signal to the scanning drive means 15 when the power supply state to each member is switched from the power saving mode to the photographing enable mode, and the power supply circuit 15a of the scanning drive means 15 receives a signal from the control means 22. , The off voltage Voff is set for the gate driver 15b. Then, the gate driver 15b of the scanning drive unit 15 applies the off voltage Voff to all the TFTs 8 via all the lines L1 to Lx of the scanning line 5 (time T0).

  Further, the control means 22 transmits a signal to the bias power supply 14 when the power supply state to each member is switched from the power saving mode to the photographing enable mode, and the bias power supply 14 via each bias line 9 or the connection 10. A bias voltage having a predetermined voltage value is applied to each radiation detection element 7.

  Thereafter, reset processing of each radiation detection element 7 is performed. In this embodiment, at the time of this reset processing, the scanning drive unit 15 applies all the TFTs 8 via all the lines L1 to Lx of the scanning line 5. On the other hand, instead of applying a normal on-voltage, for example, +15 [V] on-voltage Von3, different on-voltages Von1, Von2, and Von3 are applied, and the on-voltages Von1, Von2, and Von3 are reset. Bias is applied from each radiation detection element 7 by increasing the voltage stepwise from the start of processing (ie, Von1 <Von2 <Von3) and controlling the voltage applied to the gate electrode 8g of the TFT 8 via each scanning line 5. The current I flowing out to the line 9 and the connection 10 is limited.

  Specifically, as shown in FIG. 9, the power supply circuit 15a of the scan driving unit 15 first sets the first on-voltage Von1 for the gate driver 15b. Then, the gate driver 15b of the scanning drive unit 15 applies the first on-voltage Von1 to all the TFTs 8 via all the lines L1 to Lx of the scanning line 5 (time T1).

  Then, after a predetermined time has elapsed, the power supply circuit 15a of the scanning drive unit 15 subsequently sets the second on-voltage Von2 for the gate driver 15b. Then, the gate driver 15b of the scanning drive unit 15 applies the second on-voltage Von2 to all the TFTs 8 via all the lines L1 to Lx of the scanning line 5 (time T2).

  Then, after a predetermined time further elapses, the power supply circuit 15a of the scan driving unit 15 subsequently sets a third on-voltage Von3 that is a normal on-voltage for the gate driver 15b. Then, the gate driver 15b of the scanning drive unit 15 applies the third on-voltage Von3 to all the TFTs 8 via all the lines L1 to Lx of the scanning line 5 (time T3).

  As described above, in this embodiment, the case where the ON voltage is raised in three stages of Von1, Von2, and Von3 will be described. However, the ON voltage may be raised in two stages, or in four or more stages. It can also be configured to be pulled up. Further, the ON voltage once increased may be decreased at an intermediate stage, and the number of stages at which the ON voltage is increased and how the voltage value is increased or decreased are appropriately determined.

  When the first on-voltage Von1 is applied to the gate electrode 8g, the TFT 8 is turned on, and excess charges (electrons in the present embodiment) accumulated in the vicinity of the first electrode 74 from each radiation detection element 7 are signal lines 6. Each leaked. On the other hand, in the vicinity of the second electrode 78, which is the opposite electrode of each radiation detection element 7, a charge (in this embodiment, positive and negative) opposite to the excess charge accumulated in the vicinity of the first electrode 74 is accumulated. However, as charges (electrons) flow out to the signal line 6, the charges (holes) flow out to the bias lines 9 and flow into the bias power source 14 through the connection 10.

  However, in the present embodiment, the voltage value of the first on-voltage Von1 that is first applied as described above is higher than the voltage value of the normal on-voltage that is the third on-voltage Von3 (for example, +15 [V]). (See FIG. 10A). Therefore, when the current flowing into the bias power supply 14 is monitored by the current detection means 43, as shown in FIG. 10B, the on-voltage (third value) of the normal voltage value is also applied when the first on-voltage Von1 is applied. When the on-voltage Von3) is applied, the current I flowing from the second electrode 78 of each radiation detection element 7 into the connection 10 of the bias line 9 rises in the same manner, but when the first on-voltage Von1 is applied. In (solid line), the current I stops increasing at a value lower than that when the normal voltage ON voltage is applied (the one-dot chain line), and starts to gradually decrease.

  Subsequently, when the voltage value of the on-voltage applied to all the TFTs 8 through all the lines L1 to Lx of the scanning line 5 is raised to the second voltage value Von2 (see FIG. 11A). As shown in FIG. 11B, the current I flowing into the connection 10 of the bias line 9 rises again. However, in this case as well, the voltage value of the applied second on-voltage Von2 is lower than the voltage value of the normal on-voltage that is the third on-voltage Von3 (for example, +15 [V]). When the ON voltage of the value is applied (one-dot chain line), the current I stops increasing at a lower value and begins to decrease gradually.

  Finally, when the voltage value of the on voltage applied to all the TFTs 8 through all the lines L1 to Lx of the scanning line 5 is raised to the third voltage value Von3 which is a normal on voltage ( As shown in FIG. 12A and FIG. 12B, the current I flowing into the connection 10 of the bias line 9 rises again. However, in this case, each radiation detection element 7 is between time T1 and time T2 when the first on-voltage Von1 is applied and between time T2 and time T3 when the second on-voltage Von2 is applied. A lot of extra charge has already flowed out.

  Therefore, even when the third on-voltage Von3, which is a normal on-voltage, is applied, the current I does not rise to the peak value when the normal on-voltage is applied (one-dot chain line). It becomes a peak at a lower value and then decreases.

  Even if extra charges flow out from each radiation detection element 7, dark charges continue to be generated in each radiation detection element 7 due to thermal excitation or the like, as described above, so that the current I decreases to 0 [A]. Instead, as shown in FIG. 12 (B), the current decreases only to the amount of current Id corresponding to the sum of dark charges flowing out from each radiation detection element 7.

  Further, the current amount I of the current flowing through the connection 10 of the bias line 9 detected by the current detection means 43 in this way corresponds to the sum of the dark charges flowing out from each radiation detection element 7 in the absence of accumulated charges. It is also possible to configure so that each TFT 8 is turned off by switching the voltage applied to all the TFTs 8 from the third on-voltage Von3 to the off-voltage Voff when the amount Id or a value close thereto is reduced.

  However, in the present embodiment, in the case of the reset process of the radiation detection element 7 performed immediately before radiographic imaging, the current amount I of the current flowing through the connection 10 of the bias line 9 by the current detection unit 43 is described later. In order to make it easier to monitor the change in the current amount I of the current flowing through the connection 10 of the bias line 9, the scanning is performed in order to detect the start of radiation irradiation to the radiographic imaging apparatus 1. The driving unit 15 applies the third on-voltage Von3 to all the TFTs 8 via all the lines L1 to Lx of the scanning line 5 at time T3, and then applies the voltage applied to all the TFTs 8 to the third on-voltage. Instead of switching from Von3 to off-voltage Voff, as shown in FIG. 9, the on-voltage applied to the TFT 8 is lowered to the fourth voltage value Von4 when a predetermined time has elapsed (time T4). Going on.

  Then, the reduced fourth on-voltage Von4 is continuously applied to each TFT 8 via each scanning line 5, and at the time when the start of radiation irradiation to the radiation image capturing apparatus 1 is detected (time T5). The voltage applied to all TFTs 8 is switched from the fourth on-voltage Von4 to the off-voltage Voff. Hereinafter, this point will be described.

  The start of radiation irradiation (time T5) to the radiation image capturing apparatus 1 can be detected by attaching a radiation sensor or the like for detecting the radiation dose to the radiation image capturing apparatus 1, for example. In the embodiment, as described above, the radiation image capturing apparatus 1 itself detects the change in the current amount I of the current flowing through the connection 10 of the bias line 9 by the current detection means 43.

  That is, when the radiation image capturing apparatus 1 is irradiated with radiation, the irradiated radiation is converted into an electromagnetic wave of another wavelength such as visible light by the scintillator 3, and the electromagnetic wave is incident on the radiation detection element 7 directly below. The incident electromagnetic wave reaches the i layer 76 (see FIG. 5) of the radiation detection element 7, and electron-hole pairs are generated in the i layer 76.

  A predetermined potential gradient is formed in the radiation detection element 7 by the bias voltage applied from the bias power supply 14 via the bias line 9 and the like, and therefore, among the electron-hole pairs generated in the radiation detection element 7 One charge (electrons in this embodiment) moves to the first electrode 74 side. In addition, the other charge (hole in this embodiment) having the same amount as the one charge moves to the second electrode 78 side of the radiation detection element 7.

  At that time, if the TFT 8 is in the ON state, electrons flow out from the first electrode 74 of the radiation detection element 7 through the TFT 8 to the signal line 6, and accordingly, the same amount of holes as the radiation detection element. 7 flows out from the second electrode 78 to the bias line 9, flows through the connection 10, and is detected by the current detection means 43. As described above, when radiation irradiation to the radiographic imaging apparatus 1 is started, the current amount I of the current flowing through the connection 10 of the bias line 9 increases, so that the bias line 9 detected by the current detection unit 43 is detected. By monitoring the change in the current amount I of the current flowing through the connection 10 and detecting that the current amount I has increased, it is possible to detect the start of radiation irradiation on the radiographic imaging apparatus 1.

  Therefore, as shown in FIG. 9, after the third on-voltage Von3 is applied to all the TFTs 8 at time T3, all the TFTs 8 are continuously detected until the start of radiation irradiation to the radiation imaging apparatus 1 is detected. It is also possible to configure so that the voltage applied to is maintained at the third on-voltage Von3.

  However, in the manufacturing stage of the radiation detection element 7, when the TFT 8 is turned on, an abnormal radiation detection element 7 in which a current flows as if the first electrode 74 and the second electrode 78 are connected by a conducting wire. Will be formed. If a high third ON voltage Von3 is continuously applied to the TFT 8 in such a situation, only a small current corresponding to the dark charge generated in the normal radiation detection element 7 flows, but this is abnormal. In the radiation detection element 7, a large current flows as if it is conducting, so that the power of the battery 41 is wasted.

  Therefore, in the present embodiment, as shown in FIG. 9, the scanning drive unit 15 applies the third on-voltage Von3 to all the TFTs 8 via all the lines L1 to Lx of the scanning line 5 at time T3. The on-voltage is applied to the TFT 8 even after the application, and the on-voltage is lowered to the fourth voltage value Von4 when a predetermined time has elapsed (time T4).

  The fourth on-voltage Von4 is a radiation detecting element in which the amount of on-current that can flow through the TFT 8 when the fourth on-voltage Von4 is applied to the gate electrode 8g of the TFT 8 to turn on the TFT 8 is normal. 7 is set to a voltage value that is equal to or slightly larger than the amount of leakage current that includes dark current.

  Therefore, a slight current corresponding to the dark charge flows out from the normal radiation detection element 7, and the current flowing out from the abnormal radiation detection element 7 also flows to the normal radiation detection element 7. The amount of leakage current including dark current can be reduced to the same amount. Then, the current I flowing in the connection 10 of the bias line 9 can be reduced to a value close to the current amount Id (see FIG. 12B) corresponding to the sum of dark charges flowing out from each radiation detection element 7. Therefore, it is possible to suppress the consumption of the power of the battery 41 and prevent the battery 41 from being consumed.

  Further, by continuing to apply the fourth on-voltage Von4 to the TFT 8 until radiation irradiation is started, dark charges generated in each radiation detection element 7 until radiation irradiation is started are detected by each radiation. Since it flows out of the element 7 and is removed, it is possible to accurately remove at least noise components generated before the start of radiation irradiation from the finally obtained image data.

  As shown in FIG. 13, the start of radiation irradiation to the radiographic imaging apparatus 1 is detected by increasing the current amount I of the current flowing through the connection 10 of the bias line 9 detected by the current detection means 43. Then, at that time (time T5), as shown in FIG. 9, the voltage applied to the gate electrodes 8g of all TFTs 8 is simultaneously switched from the fourth on-voltage Von4 to the off-voltage Voff.

  When it is detected that radiation irradiation is started at time T5 and the off voltage Voff is applied to the gate electrode 8g of each TFT 8, each TFT 8 is turned off, and the electric charge almost flows out from each radiation detection element 7. No longer.

  In addition, after time T5, radiation irradiation continues to the radiation image capturing apparatus 1 for capturing a radiation image, and electron-hole pairs continue to be generated in the radiation detection element 7.

  The electron-hole pairs generated in the radiation detection element 7 are separated by electrons moving to the first electrode 74 side and holes moving to the second electrode 78 side due to the potential gradient. Since it cannot flow out, it is accumulated in the radiation detection element 7. In each radiation detection element 7, the energy of the radiation that has passed through the subject and applied to the radiation detection element 7 (in this embodiment, the radiation of the electromagnetic waves converted by the scintillator 3 is applied to the scintillator 3. The charge is proportional to the energy.

  When the radiation irradiation is completed, as shown in FIG. 14, the scanning drive unit 15 now turns on the voltage Von for reading signals from the gate driver 15b (normally the same as the third voltage value Von3 in this embodiment). The lines L1 to Lx of the scanning line 5 to which the (on voltage) is applied are sequentially switched (that is, scanned) to read out the accumulated charges from each radiation detection element 7.

  At that time, when the on-voltage Von is applied to the gate electrode 8g of the TFT 8 connected to each of the lines L1 to Lx of the scanning line 5, the electrons accumulated in the first electrode 74 of the radiation detection element 7 pass through the TFT 8. The signal is emitted to the signal line 6, converted into image data by charge-voltage conversion and amplification by the readout circuit 17 (see FIG. 7 etc.), and sequentially converted into digital value image data by the A / D converter 20. And stored in the storage means 40.

  On the other hand, in accordance with the outflow of electrons from the first electrode 74 of the radiation detection element 7, the accumulated holes flow out from the second electrode 78 of the radiation detection element 7 to the bias line 9 and flow through the connection 10. It flows into the bias power source 14. Note that when reading out the charges from the radiation detection element 7, it is not necessary to detect the current amount I of the current flowing through the bias line 9 and the connection 10, so the control means 22 switches the switch of the current detection means 43. The both terminals of the resistor of the current detection means 43 are short-circuited in the on state.

  Thereafter, dark reading processing or the like is performed as necessary. That is, as described above, in the radiographic imaging device 1 of the present embodiment, irradiation of radiation is started, and the fourth on-voltage Von4 applied to the gate electrode 8g of each TFT 8 is switched to the off-voltage Voff (time). Until T5), the dark charge generated in each radiation detection element 7 flows out because the TFT 8 is in an ON state, and at least noise components generated before the start of radiation irradiation are removed from the image data.

However, after the voltage is switched to the off voltage Voff at time T5 and each TFT 8 is turned off, the dark charges generated in each radiation detection element 7 are accumulated in each radiation detection element 7. The dark charges accumulated in each radiation detection element 7 are read out from the radiation detection elements 7 for each of the lines L1 to Lx of the scanning line 5 (time T6 _{1 to} T6 _x ). Are read out together with the image data.

Therefore, the image data for each radiation detection element 7, dark charge accumulated in each radiation detection element 7 from the time T5 to the time period ΔT ₁ ~ΔT _x to the read start time T6 ₁ to T6 _x of each line The offset corresponding to each is included. By subtracting this offset from the image data, image data corresponding to the true charge generated by the irradiation of radiation can be obtained. The process for calculating the offset is the dark reading process.

  In the dark reading process, when the reading process of the image data from each radiation detection element 7 up to the line Lx which is the final line of the scanning line 5 is completed, first, the reset process of each radiation detection element 7 is performed in the same manner as described above. Done.

  In the reset process, the voltage applied to each TFT 8 is switched from the off voltage Voff to the first on voltage Von1 at time T7, and the on voltage is switched from the first voltage value Von1 to the second at time T8, which is not shown in FIG. The voltage is increased to the voltage value Von2, and the on-voltage is increased from the second voltage value Von2 to the third voltage value Von3, which is a normal on-voltage value, at time T9, and applied to each TFT 8 at time T10. Is reduced from the third on-voltage Von3 to the fourth on-voltage Von4. Then, the voltage applied to each TFT 8 at time T11 is switched from the fourth on-voltage Von4 to the off-voltage Voff.

When the voltage is switched to the off voltage Voff at time T <b> 11 and each TFT 8 is turned off, thereafter, the dark charges generated in each radiation detection element 7 are accumulated in each radiation detection element 7. In the dark reading process, the radiation image capturing apparatus 1 is not irradiated with radiation, and the lines L1 to Lx of the scanning line 5 are left for the same periods ΔT _{1 to} ΔT _x as in the case of radiation image capturing, Dark charges are accumulated in each radiation detection element 7.

The dark charges accumulated in each radiation detection element 7 in each period ΔT _{1 to} ΔT _x in the dark reading process are the dark charges accumulated in each radiation detection element 7 in each period ΔT _{1 to} ΔT _x at the time of radiographic imaging. Since the respective amounts should be equal, after each period ΔT _{1 to} ΔT _x elapses, the scanning line 5 that applies the signal readout on-voltage Von from the gate driver 15b of the scanning driving means 15 at the same timing as described above. The lines L1 to Lx are sequentially switched (that is, scanned), the dark charges accumulated from the respective radiation detection elements 7 are read out, and the read circuit 17 performs charge voltage conversion and amplification to perform the same processing as described above. These are stored in the storage means 40 as dark read values.

  The dark reading value obtained in this way can be used as an offset as it is, and for example, the above-described dark reading processing is performed a plurality of times to obtain each radiation detection element 7. It is also possible to configure such that an average value of dark reading values for a plurality of times and the like are used as an offset amount. By performing the dark reading process in this way, it is possible to accurately acquire an offset for correcting the image data.

  Further, as described above, the reset processing of each radiation detection element 7 unique to the present invention changes the power supply state to each member of the radiation image capturing apparatus 1 from the power saving mode to the image capture possible mode for radiation image capturing. Not only when switching, but also in reset processing for dark reading processing (see times T7 to T11 in FIG. 14) and the like.

  As described above, according to the radiographic image capturing apparatus 1 according to the present embodiment, on voltages of different voltage values Von1, Von2, and Von3 are applied, and the on voltages Von1, Von2, and Von3 are stepped from the start of reset processing. Thus, the voltage applied to the gate electrode 8g of the TFT 8 via each scanning line 5 is controlled.

  For this reason, as shown in FIG. 12B, the current I flowing out from each radiation detection element 7 to the bias line 9 and the connection 10 is limited, and the current amount I of the current flowing through the bias line 9 and the connection 10 is reset. Sometimes the peak is lower than when a normal on-voltage is applied to each TFT 8 from the beginning (see the dashed line in the figure). Therefore, the reset process of the radiation detection element 7 is repeated, and it is possible to reliably reduce the probability that the connection line 10 and the like are disconnected by repeating a large amount of current flowing through the bias line 9 and the connection line 10. It becomes possible to prevent disconnection of the connection 10 or the like.

  In addition, since it is not necessary to repeat the reset process of the radiation detection element 7 more frequently than necessary, it is possible to prevent the battery power consumption by accurately preventing the power consumption of the battery from increasing by repeating the reset process. It becomes possible. Furthermore, if all the TFTs 8 are turned on simultaneously and the reset processing of each radiation detection element 7 is performed at the same time, it is possible to detect all radiation while ensuring sufficient time to remove excess charges from each radiation detection element 7. The time required for the reset process of the element 7 can be shortened.

[Second Embodiment]
In the radiographic imaging apparatus 1 according to the first embodiment described above, the voltage value of the on-voltage applied to each TFT 8 from the scanning drive unit 15 via each line L1 to Lx of the scanning line 5 is the first voltage value Von1. A case where the current I flowing from each radiation detection element 7 to the bias line 9 or the connection line 10 is limited by changing (increasing) stepwise from the first to the third voltage value Von3 through the second voltage value Von2 will be described. did.

  However, as another method of controlling the voltage I applied to the TFT 8 to limit the current I flowing from each radiation detection element 7 to the bias line 9 or the connection line 10, the scanning drive means 15 supplies the scanning line 5. From each radiation detection element 7, the pulse width and duty ratio of the on-voltage applied to each TFT 8 via each line L 1 to Lx are modulated, and an on-voltage with a short pulse width is applied multiple times. It is also possible to limit the current I flowing out to the bias line 9 and the connection 10. In the radiographic imaging device according to the second embodiment, a case where the current I flowing out to the bias line 9 and the connection 10 is limited in this way will be described.

  In the radiographic image capturing apparatus according to the second embodiment, the configuration of each means and the like is the same as in the case of the first embodiment, and will be described with the same reference numerals as those in the first embodiment. In the first embodiment, each voltage as shown in FIG. 9 is applied from the scan driving means 15 to the gate electrode 8g of each TFT 8. However, in this embodiment, each TFT 8 is supplied from the scan driving means 15. The ON voltage Von having a short pulse width as shown in FIG. 15 is applied to the gate electrode 8g a plurality of times.

  In the present embodiment, the voltage value Von of the on-voltage is applied with the voltage value Von3 of the normal on-voltage in the first embodiment (equal to the on-voltage Von for signal reading). However, it is possible to apply an on-voltage having a voltage value other than this.

  In the present embodiment, when the scanning driving unit 15 receives a signal transmitted by the control unit 22 by switching the power supply state to each member of the radiographic imaging apparatus from the power saving mode to the imaging possible mode, for example, FIG. As shown, an off voltage Voff of, for example, −10 [V] is applied from the gate driver 15b to the gate electrodes 8g of all TFTs 8 through all the lines L1 to Lx of the scanning line 5 (time t0).

  Then, the scanning drive unit 15 applies the on-voltage Von to the gate electrodes 8g of all the TFTs 8 via all the lines L1 to Lx of the scanning line 5 (time t1), and after a predetermined time has elapsed (that is, in advance) After the application of the ON voltage Von having the set pulse width is completed), the voltage applied to the gate electrode 8g of the TFT 8 is switched from the ON voltage Von to the OFF voltage Voff (time t2).

  Thereafter, the scanning drive unit 15 repeats switching between the on-voltage Von and the off-voltage Voff of the voltage applied to the gate electrode 8g of the TFT 8 by a preset number of times (a plurality of times) in this embodiment (time t3). ~ T7).

  Thus, when the voltage applied to the gate electrode 8g of the TFT 8 is switched between the on-voltage Von and the off-voltage Voff, first, the on-voltage Von is applied to the gate electrode 8g of the TFT 8 at time t1, and the TFT 8 is turned on. Then, excess charges (electrons in this embodiment) accumulated in the vicinity of the first electrode 74 of each radiation detection element 7 flow out to the signal line 6 via the TFT 8.

  On the other hand, in the vicinity of the second electrode 78, which is the opposite electrode of each radiation detection element 7, a charge (in this embodiment, positive and negative) opposite to the excess charge accumulated in the vicinity of the first electrode 74 is accumulated. However, as charges (electrons) flow out to the signal line 6, the charges (holes) flow out to the bias lines 9 and flow into the bias power source 14 through the connection 10.

  Therefore, when the current flowing into the bias power source 14 is monitored by the current detection means 43, the current I flowing from each radiation detection element 7 into the connection 10 of the bias line 9 increases as shown in FIG. When the on-voltage Von is continuously applied to the gate electrode 8g of the TFT 8, as shown by the one-dot chain line in the figure, the bias line 9 is connected from each radiation detection element 7 as in the case of the conventional radiographic apparatus. The current I flowing into the connection 10 continues to rise and reaches a maximum value.

  However, in the present embodiment, the voltage applied to the gate electrode 8g of the TFT 8 is changed from the on voltage Von to the off voltage Voff before the current I flowing from each radiation detection element 7 into the connection 10 of the bias line 9 reaches the maximum value. When the voltage is switched to the off voltage Voff at time t2 and the TFT 8 is turned off, the flow of extra electrons flowing from the radiation detecting elements 7 to the signal line 6 through the TFT 8 is cut off. Being stopped. Accordingly, the flow of excess holes flowing out from each radiation detection element 7 to the bias line 9 and the connection 10 is stopped, and the current I flowing from each radiation detection element 7 into the connection 10 of the bias line 9 starts to decrease.

  When the voltage applied to the TFT 8 is switched to the on voltage Von, the current I flowing through the connection 10 of the bias line 9 increases (time t3, t5, t7), and the voltage applied to the TFT 8 is switched to the off voltage Voff. When this occurs, excess charge accumulated in each radiation detection element 7 is released while repeating the phenomenon that the current I flowing through the connection 10 of the bias line 9 decreases (time t4, t6).

  Also in the present embodiment, as described above, since dark charges continue to be generated in each radiation detection element 7 due to thermal excitation or the like, the current I does not decrease to 0 [A], and as shown in FIG. Only the current amount Id corresponding to the sum of dark charges flowing out from the radiation detection element 7 is reduced. Therefore, the current amount I of the current flowing through the connection 10 of the bias line 9 detected by the current detection means 43 decreases to a current amount Id corresponding to the sum of dark charges flowing out from each radiation detection element 7 or a value close thereto. At this point, the switching between the on voltage Von and the off voltage Voff of the voltage applied to all TFTs 8 can be completed.

  Also in this embodiment, in the reset process of the radiation detection element 7 other than the case performed immediately before radiographic image capturing, the scanning drive unit 15 determines that the current amount I of the current flowing through the connection 10 of the bias line 9 is each radiation detection. When the current amount Id corresponding to the sum of the dark charges flowing out from the element 7 decreases to a value close to the current amount Id, the switching between the on-voltage Von and the off-voltage Voff of the voltages applied to all the TFTs 8 is finished. The voltage applied to all TFTs 8 is switched to the off voltage Voff.

  However, in the present embodiment as well as in the first embodiment, in the case of the reset process performed immediately before radiographic imaging, the voltage applied between all the TFTs 8 is between the on voltage Von and the off voltage Voff. When the switching in (1) is finished (see time t8 in FIG. 15), the voltage applied to the TFT 8 is not switched to the off-voltage Voff, and the fourth on-state, which is the reduced on-voltage in the first embodiment described above, is used. An on voltage Von4 having the same voltage value as the voltage Von4 is applied to the TFT8.

  Then, the reduced fourth on-voltage Von4 is continuously applied to each TFT 8 via each scanning line 5 until radiation irradiation is started to the radiation imaging apparatus 1 at time t9. It has become. The purpose and effect, the voltage value to be set as the fourth on-voltage Von4, and the like are exactly the same as those in the first embodiment described above.

  In addition, the start of radiation irradiation (time t9) to the radiographic imaging apparatus 1 is detected by, for example, a radiation sensor attached to the radiographic imaging apparatus 1, or the bias line 9 by the current detection unit 43 is detected. The detection by monitoring the change in the current amount I of the current flowing through the connection 10 is also as described in the first embodiment.

  Furthermore, in the reset process of each radiation detection element 7 before radiographic imaging, the readout process of image data from each radiation detection element 7, or the subsequent dark reading process, the reset process of each radiation detection element 7 and each Controlling the voltage applied to the gate electrode 8g of the TFT 8 at the same timing as the process of reading image data from the radiation detection element 7 is also the same as the control described in the first embodiment (see FIG. 14). Done.

  As described above, according to the radiographic imaging device according to the present embodiment, when the radiation detection element 7 is reset, the pulse width is long as in the conventional method described in Patent Document 4 described above. The on-voltage Von is not applied to the TFT 8 serving as the switching means only once, but the pulse width and duty ratio of the on-voltage Von applied to the TFT 8 are modulated, and the on-voltage Von applied by such a conventional method. The voltage applied to the TFT 8 is controlled so that the ON voltage Von having a pulse width shorter than the above pulse width is applied to the TFT 8 and the ON voltage Von is applied to the TFT 8 a plurality of times.

  Therefore, as shown in FIG. 16, the current I flowing out from each radiation detection element 7 to the bias line 9 or the connection 10 is limited, and the current amount I of the current flowing through the bias line 9 or the connection 10 is determined by each TFT 8 during the reset process. The peak becomes lower than when a normal on-voltage is continuously applied to (see the one-dot chain line in the figure). Therefore, the reset process of the radiation detection element 7 is repeated, and it is possible to reliably reduce the probability that the connection line 10 and the like are disconnected by repeating a large amount of current flowing through the bias line 9 and the connection line 10. It becomes possible to prevent disconnection of the connection 10 or the like.

  In addition, since it is not necessary to repeat the reset process of the radiation detection element 7 more frequently than necessary, it is possible to prevent the battery power consumption by accurately preventing the power consumption of the battery from increasing by repeating the reset process. It becomes possible. Furthermore, if all the TFTs 8 are turned on simultaneously and the reset processing of each radiation detection element 7 is performed at the same time, it is possible to detect all radiation while ensuring sufficient time to remove excess charges from each radiation detection element 7. The time required for the reset process of the element 7 can be shortened.

[Third Embodiment]
In the radiographic imaging devices according to the first and second embodiments described above, the timing at which the voltage value of the on-voltage applied to the gate electrode 8g of the TFT 8 is increased from Von1 to Von2 and Von3 (first embodiment), The description has been made on the assumption that the pulse width of the ON voltage Von and the like (second embodiment) are experimentally obtained in advance. Even in those cases, the advantageous effects can be effectively exhibited.

  However, for example, after the control unit 22 switches the power supply state to each member of the radiographic imaging apparatus from the power saving mode (sleep mode) to the radiographable mode (wake up mode), the reset processing of the radiation detection element 7 is performed. If the time until the process is long, generally, the amount of extra charge such as dark charge generated and accumulated in each radiation detection element 7 increases, and if it is shorter, the amount of extra charge decreases.

  For this reason, after the supply state of power to each member is switched to the imaging enable mode, the radiation detection element 7 flows out to the bias line 9 or the connection 10 depending on the length of time until the reset process of the radiation detection element 7 is performed. The current amount I of the current increases or decreases.

  Further, for example, if the ratio of the subject to be subjected to radiographic imaging to the radiation incident surface R (see FIG. 1) of the radiographic image capturing apparatus 1 is small, the radiation directly reaches the radiation incident surface R without passing through the subject. Increase the percentage of In this way, in the radiation detection element 7 corresponding to the part where the radiation directly reaches the radiation incident surface R, many electron-hole pairs are generated, and all of the electron-hole pairs generated in the reading process are not completely read out. In the reset process in the dark reading process performed in step 1, a relatively large amount of charge may flow out to the bias line 9 or the connection 10.

  However, if the ratio of the subject to the radiation incident surface R (see FIG. 1) of the radiographic image capturing apparatus 1 is large, for example, like X-ray imaging of the chest, radiation directly reaches the radiation incident surface R without passing through the subject. As a result, the ratio of the portion that receives strong radiation decreases, and in the reset process in the dark reading process, only a small amount of charge flows out to the bias line 9 and the connection line 10 as compared with the above case.

  Thus, the current amount I of the current flowing out from each radiation detection element 7 to the bias line 9 and the connection 10 varies depending on the situation of the radiographic apparatus.

  Therefore, in the third embodiment, the scanning drive unit 15 determines the scanning line 5 based on the current flowing through the connection 10 of the bias line 9 detected by the current detection unit 43 when the radiation detection element 7 is reset. The ON voltage applied to each TFT 8 via each line L1 to Lx is controlled to limit the current flowing out from each radiation detection element 7 to the bias line 9 or connection 10.

  Specifically, for example, a predetermined threshold value is set in advance for the current amount I of the current flowing through the connection 10 of the bias line 9 detected by the current detection means 43. For example, in the second embodiment, scanning is performed. When the current amount I of the current flowing through the connection 10 of the bias line 9 output from the current detection means 43 reaches this threshold value, the driving means 15 switches the on voltage Von applied to the TFT 8 to the off voltage Voff, and When the current amount I of the current flowing through the connection 10 of the line 9 decreases, the on-voltage Von is newly applied to the TFT 8, and when the current amount I of the current flowing through the connection 10 of the bias line 9 rises again and reaches the threshold value, The on voltage Von applied to the TFT 8 is switched to the off voltage Voff.

  As described above, the control is performed so that the voltage applied to the TFT 8 via the lines L1 to Lx of the scanning line 5 is switched between the on-voltage Von and the off-voltage Voff. The current flowing out to the line 9 and the connection 10 is limited.

  Also in the first embodiment described above, for example, when the current amount I of the current flowing through the connection 10 of the bias line 9 that has once increased by applying the first on-voltage Von1 to the TFT 8 is reduced to a predetermined amount. The voltage applied to the TFT 8 is raised to the second on-voltage Von2, and when the amount I of the current flowing through the connection 10 of the bias line 9 that has risen again decreases to a predetermined amount, the voltage applied to the TFT 8 is increased to the third voltage. Increase to ON voltage Von3.

  As described above, the on-voltage Von applied to the TFT 8 via the lines L1 to Lx of the scanning line 5 is controlled to be increased stepwise in accordance with the current amount I of the current flowing through the connection 10 of the bias line 9. By doing so, the current flowing out from each radiation detection element 7 to the bias line 9 or the connection 10 can be limited.

  As described above, the radiographic imaging apparatus according to the present embodiment can also achieve the same effects as the radiographic imaging apparatuses according to the first and second embodiments.

  In addition, according to the radiographic image capturing apparatus according to the present embodiment, the amount of extra charge accumulated in each radiation detecting element 7 that changes according to the situation of the radiographic image capturing apparatus, that is, the current detecting means 43 detects the amount. Based on the current amount I of the current flowing through the bias line 9 and the connection line 10, the on-voltage applied to the gate electrode 8g of each TFT 8 via each line L1 to Lx of the scanning line 5 is accurately controlled to detect each radiation. It is possible to reliably limit the current flowing from the element 7 to the bias line 9 and the connection 10 according to the situation of the radiographic apparatus.

[Radiation imaging system]
In the radiographic imaging device 1 according to the first to third embodiments, a radiation sensor is provided, or the current detection unit 43 that detects the current amount I of the current flowing through the connection 10 of the bias line 9 is utilized. The case where the start and the end of the radiation irradiation with respect to the radiation image capturing apparatus 1 are detected has been described. However, in many cases, the radiation imaging apparatus 1 is not provided with the radiation sensor or the current detection means 43.

  In such a case, the radiation image capturing apparatus 1 can be configured to transmit a signal notifying the start or end of radiation irradiation to the radiation image capturing apparatus 1 from a radiation generator that irradiates the radiation image 1 or the like. .

  Further, in an actual radiation generator, it often takes about 1 second from the start of the radiation source of the radiation generator to the irradiation of radiation. For this reason, it is possible to configure the radiographic imaging apparatus 1 to perform a reset process before radiographic imaging using the time from activation of the radiation source to irradiation.

  Below, the radiographic imaging system for implement | achieving it is demonstrated. FIG. 17 is a diagram illustrating an overall configuration of the radiographic image capturing system according to the present embodiment. As shown in FIG. 17, the radiographic imaging system 50 includes, for example, an imaging room R1 that irradiates radiation and images a subject that is a part of a patient (not shown), and an operator such as a radiologist radiates radiation to the subject. It is arrange | positioned in front chamber R2 which performs operations, such as irradiation.

  In the present embodiment, in the imaging room R1, a Bucky device 51 that can be loaded with the above-described radiographic image capturing device 1 (portable radiographic image capturing device 1) or an X-ray tube (not shown) that generates radiation to irradiate a subject. A radiation source 52 of the radiation generating apparatus, a radio access point (base station) 54 provided with a wireless antenna 53 that relays these communications when the radiographic imaging apparatus 1 and other apparatuses communicate wirelessly, and the like. ing.

  Further, in the front chamber R2, an operation console 56 of a radiation generation apparatus provided with an irradiation start switch 55 for instructing the start of irradiation of radiation from the radiation source 52, and a radiation image capturing apparatus 1 described later. A tag reader 57 and the like for detecting a tag are provided. The console 56 and the tag reader 57 of the radiation generating apparatus are connected to a console 58 provided outside the imaging room.

  The console 58 performs image processing using image data acquired by the radiation image capturing system 50, a dark read value, and the like, and generates a radiation image. It is possible to provide the console 58 in the front chamber R2. The console 58 is connected to storage means 59 composed of a hard disk or the like.

  The configuration of the radiographic image capturing apparatus 1 is as described in the first to third embodiments. In the present exemplary embodiment, the radiographic image capturing apparatus 1 further includes a tag (not shown). In this embodiment, a tag called a so-called RFID (Radio Frequency IDentification) tag is used as the tag, and the tag stores a control circuit that controls each part of the tag and a storage that stores unique information of the radiographic imaging apparatus 1. The part is built in compactly. The unique information includes, for example, a cassette ID, scintillator type information, size information, resolution, and the like as identification information assigned to the radiation image capturing apparatus 1.

  In addition, the radiographic image capturing apparatus 1 can be used in a so-called independent state that is not loaded in the bucky device 51. That is, the radiation image capturing apparatus 1 is arranged in a single state, for example, on a support stand provided in the capturing room R1 or a bucky apparatus 51B for supine photographing as shown in FIG. 1) and the patient's hand as the subject can be placed on the head, or can be used, for example, inserted between the patient's waist or legs lying on the bed and the bed. ing. In this case, for example, 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.

  The bucky device 51 is provided with a cassette holding portion 51a for holding the radiographic image capturing device 1 in a predetermined position, and the radiographic image capturing device 1 can be loaded into the cassette holding portion 51a. Further, in the present embodiment, as the bucky device 51, there are provided a bucky device 51A for standing position shooting and a bucky device 51B for standing position shooting. In the present embodiment, each of the bucky devices 51A and 51B is connected to the operation console 56 of the radiation generating device via a cable, a wireless access point (base station) 54, and the like.

  In the imaging room R1, at least one radiation source 52 including an X-ray tube that irradiates the radiation image capturing apparatus 1 with radiation through a subject is provided. In the present embodiment, one radiation source 52A is shared by the bucky devices 51A and 51B for standing position shooting and standing position shooting. It should be noted that it is also possible to configure each of the bucky devices 51A and 51B so that different radiation sources are associated with each other.

  The radiation source 52A is arranged suspended from the ceiling of the imaging room R1, for example, and is set up based on an instruction from an operation console 56 (to be described later) at the time of imaging. And the direction of the radiation is adjusted so that the radiation direction is in a predetermined direction.

  Further, in the present embodiment, a portable radiation source 52B that is not associated with the standing-up imaging device 51A or the lying-up imaging device 51B is also provided, and the portable radiation source 52B has an imaging function. It can be carried to any place in the room R1, and radiation can be emitted in any direction.

  In the present embodiment, the portable radiation source 52B is also set up based on an instruction from the console 56. In addition to this, for example, the operator manually sets up the radiation source 52B. It is also possible to configure to set up by transmitting a radio signal from the image capturing apparatus 1 to the portable radiation source 52B.

  As the X-ray tube of the radiation source 52, a radiation source using a rotating anode X-ray tube is preferably used. An X-ray tube is often configured to generate radiation by causing an electron beam emitted from a cathode to collide with an anode. However, if an electron beam continues to collide with the same position on the anode, The anode is damaged due to the occurrence. Therefore, in the rotating anode X-ray tube, the anode is extended so that the position where the electron beam collides does not become the same position, thereby extending the life of the anode.

  The front chamber R2 is provided with an operation console 56 of a radiation generating apparatus provided with an irradiation start switch 55 for instructing start of irradiation of radiation from the radiation source 52. In FIG. 17, the console 56 and the irradiation start switch 55 are described as separate bodies, but they are not necessarily configured as separate bodies.

  The console 56 is configured by a computer including a CPU and a dedicated processor. Further, as shown in FIGS. 18A to 18C, the irradiation start switch 55 includes a rod-shaped button portion 55a and a housing portion that supports the button portion 55a so that the button portion 55a can be pressed in the direction indicated by the arrow S in the drawing. 55b. As shown in FIG. 18A, the button portion 55a includes a cylindrical portion 55a1 protruding upward from the housing portion 55b and a columnar portion 55a2 protruding further upward from the inside thereof.

  Then, as shown in FIG. 18B, when the column portion 55a2 is pushed down to the upper end portion of the cylindrical portion 55a1 by the operator and the button portion 55a is half-pressed, a predetermined radiation source 52 is supplied from the console 56. When the activation signal is received, the radiation source 52 starts to rotate by starting rotation of the anode of the X-ray tube. This activation signal is also transmitted to the radiation image capturing apparatus 1 via the wireless access point 54.

  As shown in FIG. 18C, the operator further pushes the cylindrical portion 55a1 and the column portion 55a2 of the button portion 55a of the irradiation start switch 55 to the upper end portion of the housing portion 55b. When it is fully pressed, an irradiation signal is transmitted from the console 56 to a predetermined radiation source 52. When the radiation source 52 receives the irradiation signal, the irradiation signal is emitted. Yes. This irradiation signal is also transmitted to the radiation image capturing apparatus 1 via the wireless access point 54.

  Instead of transmitting the activation signal or the irradiation signal from the operation console 56 or the irradiation start switch 55 to the radiographic image capturing apparatus 1 via the wireless access point 54, the irradiation start switch 55 is pressed halfway or fully. When the irradiation start switch 55 is half-pressed, an activation signal (or a signal indicating that the radiation source 52 has been activated) is transmitted to the radiographic image capturing apparatus 1, and the irradiation start switch 55 is fully activated. It is also possible to provide a button operation detecting means 60 that transmits an irradiation signal (or a signal indicating that radiation has been irradiated from the radiation source 52) to the radiographic imaging device 1 when pressed.

  Note that the above-described configuration of the irradiation start switch 55 is not a configuration specific to the present invention, but is a configuration widely used in an operation console of a normal radiographic image capturing system. Usually, the button portion 55a is half-pressed. It is configured so that it can be fully pressed after about 1 second has elapsed.

  Further, a tag reader 57 (see FIG. 17) for exchanging information with the radiographic imaging apparatus 1 using the RFID technology described above is installed in the vicinity of the entrance of the front chamber R2, and the tag reader 57 is connected to the front chamber R2. In addition, the radiographic imaging device 1 entering or leaving the imaging room R1 is detected, and the information is transmitted to the console 58. The console 58 manages the radiation image capturing apparatus 1 existing in the image capturing room R1 and the front room R2.

  The radiographic image capturing apparatus 1 is a mode in which the power supply state of each member can be captured from the power saving mode (sleep mode) by operating the power switch 36 by an operator such as a radiographer for radiographic image capturing. It is switched to (wake up mode) and loaded into the bucky device 51.

  Then, a subject that is a part of the patient is set on the radiation incident surface R side of the radiographic imaging apparatus 1. In the radiographic image capturing system 50 of the present embodiment, the radiographic image capturing apparatus 1 does not start the reset process of each radiation detection element 7 at the stage where the power supply state to each member is switched to the image capture enable mode. As described in each embodiment of the radiation image capturing apparatus 1, the radiation detection elements 7 may be reset in stages.

  Then, when the operator moves to the console 56 of the radiation generating apparatus in the front chamber R2 and presses the button portion 55a of the irradiation start switch 55 halfway, an activation signal is transmitted from the console 56 to the predetermined radiation source 52. Then, the radiation source 52 is started by starting rotation of the anode of the X-ray tube, and this activation signal (or a signal indicating that the radiation source 52 has been activated) is operated by the console 56, the irradiation start switch 55 or the button operation. It is also transmitted from the detection means 60 to the radiographic imaging apparatus 1 via the wireless access point 54.

  When the activation signal is transmitted wirelessly via the wireless antenna 53 of the wireless access point 54 or via the cable from the wireless access point 54 and wired via the bucky device 51, control of the radiographic imaging device 1 is performed. The means 22 instructs the scanning drive means 15 to perform reset processing of each radiation detection element 7.

  In response to an instruction from the control unit 22, the scanning drive unit 15 performs the entire scanning line 5 as described in the embodiment of the radiographic imaging apparatus 1 (see particularly FIG. 9, FIG. 14, FIG. 15, etc.). An on-voltage Von having a predetermined voltage value is applied to the gate electrode 8g of the TFT 8 which is the switching means of each radiation detection element 7 via the lines L1 to Lx.

  That is, if the radiographic image capturing apparatus 1 is the radiographic image capturing apparatus according to the first embodiment, each of the on-voltages Von1 having a different voltage value to the gate electrode 8g of the TFT 8 through all the lines L1 to Lx of the scanning line 5. Von2 and Von3 are applied so that the voltage value increases stepwise. Further, if the radiographic imaging apparatus 1 is the radiographic imaging apparatus according to the second embodiment, a plurality of on-voltages Von having a short pulse width are applied to the gate electrode 8g of the TFT 8 via all the lines L1 to Lx of the scanning line 5. Apply once.

  In this embodiment, the on-voltage Von4 is applied to the gate electrode 8g of the TFT 8 through the all lines L1 to Lx of the scanning line 5 by reducing the voltage value of the on-voltage Von in any case. Keep doing.

  Then, after the operator presses the button portion 55a of the irradiation start switch 55 of the console 56 halfway, when the button portion 55a of the irradiation start switch 55 is fully pressed after a time of about 1 second has elapsed, the operator console 56 An irradiation signal is transmitted to the predetermined radiation source 52, and radiation is emitted from the radiation source 52. Further, this irradiation signal (or a signal indicating that the radiation source 52 has been irradiated) is sent from the console 56, the irradiation start switch 55 or the button operation detection means 60 to the radiographic image capturing apparatus 1 via the wireless access point 54. Sent.

  When receiving the irradiation signal transmitted from the console 56, the irradiation start switch 55, or the like, the control means 22 of the radiographic imaging apparatus 1 transmits a signal notifying the start of radiation irradiation to the scanning driving means 15. When the scanning drive unit 15 receives the signal from the control unit 22, the scanning driving unit 15 switches the on voltage Von 4 applied to the gate electrode 8 g of the TFT 8 through all the lines L 1 to Lx of the scanning line 5 to the off voltage Voff. All TFTs 8 are turned off.

  In this way, charges generated in each radiation detection element 7 are accumulated in each radiation detection element 7. Subsequent processing is performed in the same manner as the processing described in the embodiment of the radiographic imaging apparatus 1 described above. When the irradiation of radiation is completed, the scanning drive unit 15 performs, for example, as shown in FIG. While sequentially switching the lines L1 to Lx of the scanning line 5 to which the signal read-on voltage Von is applied from the gate driver 15b, the charges accumulated from the radiation detecting elements 7 are read and converted into image data and stored in the storage means 40. Remember.

  Thereafter, a dark reading process is performed. In the dark reading process, after the reset process of each radiation detection element 7 is performed, the off voltage Voff is applied to the gate electrode 8g of each TFT 8, and no radiation is irradiated. After being left for a predetermined time, the dark charge generated in each radiation detection element 7 for each of the lines L1 to Lx of the scanning line 5 is read as a dark read value at the same timing as the image data read processing and stored in the storage means 40. Is remembered.

  The image data and dark reading value for each radiation detection element 7 obtained in this way are transmitted to the console 58, an offset is calculated based on the dark reading value, and the offset is subtracted from the image data. Thus, final image data for each radiation detection element 7 is calculated, and a radiation image is generated.

  As described above, according to the radiographic image capturing system 50 according to the present embodiment, it is possible to effectively exhibit the effects of the radiographic image capturing apparatus in each of the above embodiments.

  In addition, the activation signal is transmitted to the radiation source 52 and reset processing of each radiation detection element 7 of the radiation imaging apparatus 1 is started, and the irradiation signal is transmitted to the radiation source 52 to detect radiation irradiation. There is a time of about 1 second until the voltage applied to the gate electrode 8g of the TFT 8 of each radiation detection element 7 is switched to the off voltage Voff.

  Therefore, it is possible to sufficiently discharge and remove excess charges accumulated in each radiation detection element 7, and to apply a turn-on voltage Von4 to the gate electrode 8g of the TFT 8 for a longer time than necessary to obtain a radiation image. It is possible to accurately prevent the power of the battery 41 of the photographing apparatus 1 from being wasted, and it is possible to prevent the battery 41 from being consumed.

  In the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to each of the embodiments described above, each line L1 of the scanning line 5 from the scan driving unit 15 of the radiographic image capturing apparatus 1 is performed when the radiation detection element 7 is reset. The case where the on-voltage Von (first on-voltage Von1) is simultaneously applied to all the TFTs 8 serving as switching means via Lx has been described.

  However, as shown in FIG. 3, the plurality of scanning lines 5 arranged in the detection unit P of the substrate 4 are divided into a plurality of groups such as an upper half and a lower half in the figure, and the respective scanning lines 5 are interposed. The on-state voltage Von applied to the gate electrode 8g of the TFT 8 serving as the switching means is applied at different times and simultaneously to the TFTs 8 connected to the scanning lines 5 belonging to one group to perform reset processing. It is also possible to configure.

  If comprised in this way, since each radiation detection element 7 to which TFT8 was connected to the scanning line 5 which belongs to each group will flow out the electric current I to the bias line 9 and the connection 10 at a different timing for every group, It is possible to reduce the current I of the current flowing every time.

  For this reason, the current I flowing out from each radiation detection element 7 to the bias line 9 or the connection 10 is further limited, and the peak of the current amount I of the current flowing through the bias line 9 or the connection 10 can be further reduced. Even if the reset process of the element 7 is repeated, the probability that the connection 10 or the like is disconnected can be further reduced. And it becomes possible to prevent disconnection of the connection 10 etc. in effect.

It is a perspective view which shows the radiographic imaging apparatus which concerns on each embodiment. It is sectional drawing which follows the AA line in FIG. It is a top view which shows the structure of the board | substrate which concerns on this embodiment. It is an enlarged view which shows the structure of the radiation detection element, TFT, etc. which were formed in the small area | region on the board | substrate of FIG. It is sectional drawing which follows the XX line in FIG. It is a side view explaining the board | substrate with which COF, a PCB board | substrate, etc. were attached. It is a figure showing the equivalent circuit schematic of the radiographic imaging apparatus which concerns on this embodiment. FIG. 8 is an equivalent circuit diagram for one pixel in FIG. 7. It is a graph showing the time transition of the voltage value of the voltage applied to a switch means in the radiographic imaging apparatus which concerns on 1st Embodiment. (A) It is a graph showing the state where the 1st ON voltage was applied to the switch means, (B) It is a graph showing the time change of the electric current amount which flows through the connection of the bias line detected by an electric current detection means. is there. (A) It is a graph showing the state by which the ON voltage applied to a switch means was switched to the 2nd ON voltage, (B) Time of the electric current amount of the current which flows through the connection of the bias line detected by a current detection means It is a graph showing a change. (A) It is a graph showing the state by which the ON voltage applied to a switch means was switched to the 3rd ON voltage, (B) Time of the electric current amount of the current which flows through the connection of the bias line detected by a current detection means It is a graph showing a change. It is a graph showing that the amount of current that flows out to the connection of the bias line increases due to the generation of electric charge in the radiation detection element when radiation irradiation is started. It is a timing chart of the voltage value applied to each line of a scanning line from a scanning drive means. It is a graph showing the time transition of the voltage value of the voltage applied to a switch means in the radiographic imaging apparatus which concerns on 2nd Embodiment. 16 is a graph showing a temporal change in the amount of current flowing through a bias line connection detected by a current detection unit when a voltage is applied to the switch unit as shown in FIG. It is a figure which shows the whole structure of the radiographic imaging system which concerns on this embodiment. (A) is a figure which shows the structure of an irradiation start switch, (B) is the state which the button part was half-pressed, (C) is a figure explaining the state by which it fully pressed.

Explanation of symbols

1 Radiographic imaging device (portable radiographic imaging device)
5 Scanning line 6 Signal line 7 Radiation detection element 8 TFT (switch means)
9 Bias line 14 Bias power supply 15 Scanning drive means 15a Power supply circuit 15b Gate driver 39 Antenna device (communication means)
41 Battery 43 Current detection means 50 Radiation imaging system 52 Radiation source (radiation generator)
55 Irradiation start switch (radiation generator)
56 console (radiation generator)
I current, current amount P detection unit r region Voff off voltage Von on voltage, on voltages Von1 to Von3 for signal reading on voltages having a plurality of different voltage values

Claims (11)

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; A detector comprising:
A bias line connected to each of the radiation detection elements;
A bias power source for applying a bias voltage to each radiation detection element via the bias line;
When an on-voltage is applied to the scanning line arranged and connected to each radiation detection element, a charge generated in the radiation detection element is released, and an off-voltage is applied to the connected scanning line. Switch means for accumulating charges generated in the radiation detection element in the radiation detection element;
A scanning drive unit that includes a power supply circuit and a gate driver, and controls a voltage applied to the switch unit via each scanning line;
With
A battery for supplying power to each of the above means is incorporated,
The scanning drive unit controls a voltage applied to the switch unit via each scanning line during a reset process of the radiation detection element that discharges excess charges accumulated in the radiation detection element. A portable radiographic imaging device, wherein current flowing out from each radiation detection element to the bias line is limited.   The scanning drive means applies the on voltages having a plurality of different voltage values as the on voltages to be applied to the switch means via the scanning lines during the reset process of the radiation detection element. The radiographic imaging apparatus according to claim 1, wherein the current flowing out from each radiation detection element to the bias line is limited.   In the reset process of the radiation detection element, the scan driving means increases the ON voltage applied to the switch means via each scanning line in a stepwise manner from the start of the reset process of the radiation detection element. The radiographic imaging apparatus according to claim 2, wherein the current flowing out from each radiation detection element to the bias line is limited.   The scan driving means modulates the pulse width and duty ratio of the on-voltage applied to the switch means via the scan lines during the reset process of the radiation detection element, and the switch means The radiographic imaging apparatus according to claim 1, wherein the current flowing out from each radiation detection element to the bias line is limited by applying the ON voltage a plurality of times. Current detecting means for detecting a current flowing through the bias line;
The scan driving means applies an on-voltage applied to the switch means via each scanning line based on the current flowing through the bias line detected by the current detection means during the reset process of the radiation detection element. The radiographic imaging apparatus according to any one of claims 2 to 4, wherein the current flowing out from each of the radiation detection elements to the bias line is limited.   The scanning drive means performs a process of controlling a voltage applied to the switch means via each scanning line during the reset process of the radiation detection element, and performs all the switching means via all the scanning lines. The portable radiographic image capturing apparatus according to claim 1, wherein the portable radiographic image capturing apparatus is performed simultaneously.   The scanning drive unit performs a plurality of scanning lines when a process for controlling a voltage applied to the switching unit via each scanning line is simultaneously performed on the switching unit via the scanning line. It is divided into groups, and the processing is simultaneously performed for all the switch means connected to the scanning lines belonging to one group, and is performed for all the groups of the scanning lines. Item 7. The portable radiographic image capturing device according to Item 6. Current detecting means for detecting a current flowing through the bias line;
The scanning drive unit detects that the irradiation of the radiation is started by increasing the amount of the current flowing through the bias line detected by the current detection unit. The portable radiographic imaging device according to claim 7.   When the scanning drive unit detects that the radiation irradiation has started after performing the reset process of the radiation detection element, the scanning driving unit sequentially switches the scanning lines after the radiation irradiation. Image data is read by applying an on-voltage for signal readout to each switch means via a scanning line, and when the application of the on-voltage for signal readout to each scanning line is completed, the radiation detection The radiation detection elements are controlled by controlling the voltage applied to the switch means via the scanning lines at the same timing as the resetting process of the elements and the sequential application of the on-voltage for reading the signals to the scanning lines. The portable radiographic image capturing apparatus according to claim 8, wherein dark reading processing is performed to read dark charges from the image. The portable radiographic image capturing apparatus according to any one of claims 1 to 7, further comprising a communication unit capable of communicating with outside.
A radiation generator comprising: a radiation source that irradiates radiation to the portable radiation imaging apparatus; and an operation console that activates the radiation source and includes an irradiation start switch that instructs the radiation source to start radiation irradiation; ,
With
When the scanning drive unit of the portable radiographic image capturing apparatus receives the radiation source activation signal transmitted from the console via the communication unit, it starts resetting the radiation detection element. A featured radiographic imaging system.   When the scanning drive unit of the portable radiographic imaging apparatus receives an irradiation signal of the radiation source transmitted from the console via the communication unit after performing a reset process of the radiation detection element After the irradiation of the radiation, the on-voltage for signal reading is applied to the switch means via the scanning lines while sequentially switching the scanning lines, and image data reading processing is performed. When the application of the on-voltage for reading the signal to the scanning line is finished, each scanning line has the same timing as the reset processing of the radiation detection element and the sequential processing of applying the on-voltage for reading the signal to the scanning line. A dark reading process for reading out a dark charge from each of the radiation detection elements is performed by controlling a voltage applied to the switching means via a switch. Radiographic imaging system according to 0.

Images