JP2013039208A - Radiation imaging apparatus and radiation imaging system - Google Patents

Abstract

Radiographic imaging capable of accurately displaying a preview image on a console and capable of performing a single radiographic imaging in a short time when the apparatus itself detects the start of radiation irradiation. Providing equipment.
When the control means 22 of the radiographic image capturing apparatus 1 detects that radiation irradiation has been started based on leak data dleak read out before radiographic image capturing, after passing through a charge accumulation state, A state in which the readout process is performed and the transmission process for transmitting the preview image data Dt based on the readout image data D to the console 58 is started, and at the same time, the readout process of the leak data dleak is performed once and no radiation is irradiated. If the transmission process of the preview image data Dt is not completed when the continuation of the charge accumulation state is completed after the charge accumulation state is continued in step S5, the transmission process is stopped, and then the offset data O is read. Let the process do.
[Selection] Figure 26

Description

  The present invention relates to a radiographic image capturing apparatus and a radiographic image capturing system, and more particularly to a radiographic image capturing apparatus that performs radiation image capturing by detecting radiation irradiation by the apparatus itself and a radiographic image capturing system used therefor.

  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 A so-called indirect radiographic imaging device that converts an electromagnetic wave having a wavelength and then generates a charge in a photoelectric conversion element such as a photodiode according to the energy of the converted electromagnetic wave and converts it to an electrical signal (ie, image data). Have been developed. 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 is conventionally configured as a so-called special-purpose machine that is integrally formed with a support base (see, for example, Patent Document 1). In recent years, a portable radiographic imaging apparatus in which a radiation detection element or the like is housed in a casing and can be carried has been developed and put into practical use (for example, see Patent Documents 2 and 3).

  In such a radiographic imaging apparatus, for example, as shown in FIG. 7 and the like to be described later, normally, a plurality of radiation detection elements 7 are arranged in a two-dimensional form (matrix) on the detection unit P, and each radiation detection element 7 is connected to switch means formed of thin film transistors (hereinafter referred to as TFTs) 8.

  In general, in radiographic imaging, radiation is irradiated from a radiation source of a radiation generation device to a radiographic imaging device through a predetermined imaging region (that is, the front of the chest, the lumbar vertebrae, etc.) such as the body of the subject. To be done.

  At that time, by applying an off voltage to the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning drive unit 15 of the radiographic imaging apparatus and irradiating the radiation in a state where all the TFTs 8 are in an off state, Charges generated in each radiation detection element 7 due to radiation irradiation are accurately accumulated in each radiation detection element 7.

  Then, after radiographic imaging, on-voltages are sequentially applied from the gate driver 15b to each of the lines L1 to Lx of the scanning line 5 so that the TFTs 8 are sequentially turned on, and are generated in each radiation detection element 7 by radiation irradiation. The charges accumulated in this manner are sequentially discharged to each signal line 6 and read out as image data D by each readout circuit 17.

  By the way, as described above, in order to perform radiographic image capture accurately, an off voltage is appropriately applied to each of the lines L1 to Lx of the scanning line 5 from the gate driver 15b when the radiographic image capturing apparatus is irradiated with radiation. Is applied, and it is necessary that each TFT 8 serving as the switch means is turned off.

  Therefore, for example, in a conventional dedicated-type radiographic imaging apparatus or the like, an interface is constructed with the radiation generating apparatus, and signals and the like are exchanged with each other. In many cases, the radiographic imaging apparatus is configured to irradiate radiation from a radiation source after confirming that a charge accumulation state has been established by applying an OFF voltage to.

  However, for example, when the manufacturers of the radiographic imaging device and the radiation generator are different, it may not always be easy to construct an interface between them, or the interface cannot be constructed There is also.

  When an interface is not constructed between the radiation image capturing apparatus and the radiation generating apparatus in this way, it is not known at what timing radiation is emitted from the radiation source when viewed from the radiation image capturing apparatus side. Therefore, the radiographic imaging apparatus must detect itself that the radiation has been emitted from the radiation source.

  Therefore, in recent years, various radiographic imaging apparatuses configured to detect themselves that radiation has been emitted have been developed without using such an interface between the radiographic imaging apparatus and the radiation generation apparatus. .

  For example, in the inventions described in Patent Literature 4 and Patent Literature 5, when radiation is started on the radiation imaging apparatus and charges are generated in each radiation detection element 7, each radiation detection element 7 sends each radiation detection element. The bias line 9 is provided with a current detecting means by utilizing the fact that electric charge flows out to the bias line 9 (see FIG. 7 described later) connected to 7 and the current flowing through the bias line 9 increases. It has been proposed to detect a current value of a current flowing through the inside and detect the start of radiation irradiation based on the current value.

  On the other hand, when the start of radiation irradiation is detected, after the gate driver 15b of the scanning drive unit 15 applies the off voltage to each of the lines L1 to Lx of the scanning line 5 and shifts to the charge accumulation state as described above. The on-voltage is sequentially applied from the gate driver 15b to each of the lines L1 to Lx of the scanning line 5, and the image data D is read from each radiation detection element 7.

  Also, so-called dark charges (also referred to as dark current) that are always generated by thermal excitation or the like due to the heat (temperature) of each radiation detection element 7 while each TFT 8 is in the OFF state in the charge accumulation state are each radiation. Accumulated in the detection element 7. Then, the offset due to the dark charge is superimposed on the read image data D.

  Therefore, in order to remove the offset due to the dark charge superimposed on the image data D from the read image data D, the offset data O corresponding to the offset due to the dark charge is acquired. There is a case where the offset data O is read out.

  In addition, the final radiation is obtained by performing precise image processing on the console 58 described later (see FIGS. 11 and 12 described later) based on the image data D and offset data O read by the radiation image capturing apparatus. An image is generated.

  However, for example, when the subject is not properly captured in the image, even if the radiation image is generated, the image becomes useless. Therefore, for example, after the reading process of the image data D is completed in the radiographic image capturing apparatus, the thinned data Dt is generated by thinning out the image data D at a predetermined ratio from the image data D or all the read image data D. To the console 58. The console 58 may be configured to generate and display a preview image based on the thinned data Dt.

  Then, the radiologist looks at the preview image displayed on the display unit of the console 58 and determines whether or not the radiographic image has been appropriately captured, that is, whether or not the subject is properly captured in the image. Then, the necessity of re-photographing is determined. Hereinafter, the image data D for the preview image and the thinned data Dt are collectively referred to as preview image data.

JP-A-9-73144 JP 2006-058124 A JP-A-6-342099 US Pat. No. 7,211,803 JP 2009-219538 A

  By the way, in the research by the present inventors, when the irradiation start is detected by the method described in Patent Document 4 or Patent Document 5 described above, the bias line 9 is an electrode of each radiation detection element 7. Therefore, noise generated by the current detection means is transmitted to each radiation detection element 7 via the bias line 9 and may be superimposed as noise on the image data D read from the radiation detection element 7. It has been found that there are problems that are not always easy to solve.

  As a result of various researches on other methods for detecting that radiation has been emitted by the radiographic imaging device itself, the present inventors have developed new devices and means such as current detection means as will be described later. Even if it is not used, it is possible to find several new methods that can accurately detect that radiation has been emitted by the radiographic imaging device itself by using an existing functional unit in the radiographic imaging device. It was.

  In the research conducted by the present inventors, when such a new method is adopted, the processing method suitable for the detection method described above in the offset data O reading process after the image data D reading process is performed. It has also been found that the offset data O can be read by performing the offset data O reading process.

  On the other hand, the same applies when such a new method is adopted. However, in general radiographic imaging devices and radiographic imaging systems, as described above, after the image data D is read out, the data for the preview image is stored. When transmitting to the console 58, if the reading process of the offset data O is started before the transmission of the data for the preview image is completed, problems such as noise being superimposed on the read offset data O may occur. Therefore, transmission of preview image data from the radiographic imaging apparatus to the console 58 is usually stopped halfway.

  Therefore, data for the preview image cannot be transmitted sufficiently, and even if the preview image is displayed on the console 58, the preview image is not sufficiently displayed on the console 58, and even if the radiologist looks at the preview image, There is a possibility that it may not be possible to appropriately determine whether or not the subject is properly captured in the image and whether or not re-shooting is necessary.

  Therefore, in the conventional radiographic imaging device and radiographic imaging system, in order to display all the preview images without interruption, the image data D is read out from the radiographic imaging device to the console 58 after being read out. All data transmission processing is performed to complete the transmission processing. Then, after the transmission process is completed, the offset data O is read out.

  In order to achieve this, after the image data D is read out, the radiation detection elements 7 are reset at the same time as the preview image data transmission processing is started, and the transmission processing of all data for the preview image is performed. The configuration was such that the reset processing of each radiation detection element 7 was repeated until completion.

  However, normally, in the offset data O reading process, as in the case of the image data D reading process, an off voltage is once applied from the gate driver 15b of the scanning driving unit 15 to the lines L1 to Lx of the scanning line 5. In many cases, the offset data O is read out after passing through a charge accumulation state that is applied.

  Therefore, with the above configuration, after the image data D reading process, a transmission process for transmitting all the data for the preview image is performed in parallel with the reset process of each radiation detection element 7. Then, after the transmission process of all data is completed, the charge storage state is entered and the charge storage state is continued for a predetermined time. Thereafter, the offset data O is read out.

  However, with this configuration, after the reading process of the offset data O is completed, the transmission process of the image data D and the offset data O from the radiation imaging apparatus to the console 58 is finally performed. The time from the end of the reading process of D to the end of the reading process of the offset data O to the completion of the transmission process of the image data D or the like becomes longer. Therefore, there has been a problem that the time required for one radiographic image capturing becomes long.

  The present invention has been made in view of the above problems, and when the radiation imaging apparatus itself detects the start of radiation irradiation, it is possible to accurately display a preview image on the console. It is an object of the present invention to provide a radiographic image capturing apparatus capable of performing one radiographic image capturing in a short time and a radiographic image capturing system using the same.

In order to solve the above-described problem, the radiographic imaging device of the present invention includes:
A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other, and a plurality of radiation detection elements arranged in a two-dimensional manner in each small region partitioned by the plurality of scanning lines and the plurality of signal lines A detector comprising:
Scan driving means for applying an on voltage or an off voltage to each of the scanning lines;
Switch means connected to each of the scanning lines and causing the signal lines to discharge charges accumulated in the radiation detection element when an on-voltage is applied;
A readout circuit that converts the electric charge emitted from the radiation detection element into image data and reads the image data;
The charge leaked from each radiation detection element via each switch means in a state where an off voltage is applied to each scan line from the scan driving means to turn off each switch means before radiographic image capturing. The leak data reading process for converting the data into leak data and the reset process of the radiation detection elements performed by sequentially applying an on-voltage to the scan lines from the scan driving unit are alternately performed, and the read Control means for detecting the start of radiation irradiation based on the leak data;
With
The control means includes
When the start of radiation irradiation is detected, an off voltage is applied to each scanning line from the scanning driving unit, and after passing through a charge accumulation state in which each switching unit is turned off, at least the scanning driving unit and the readout circuit are After performing control and reading processing of image data from the radiation detection element,
At the same time as starting the transmission process for transmitting preview image data based on the read image data to the console, the reset process of each radiation detection element, which is alternately performed with the read process of the leak data, is detected from the scan driving means. The on-voltage is sequentially applied to each of the scanning lines of the unit, and the leakage data reading process and the resetting process of the radiation detection elements are alternately performed.
Thereafter, in a state where no radiation is applied, an off voltage is applied to each scanning line from the scanning drive means for the same time as the charge accumulation state before the image data read processing, thereby turning off the switch means. Continue the charge accumulation state,
If the transmission processing of the preview image data is not completed when the continuation of the charge accumulation state is completed, the transmission processing is stopped and then the offset data reading processing is performed.

Moreover, the 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, and a plurality of radiation detection elements arranged in a two-dimensional manner in each small region partitioned by the plurality of scanning lines and the plurality of signal lines A detector comprising:
Scan driving means for applying an on voltage or an off voltage to each of the scanning lines;
Switch means connected to each of the scanning lines and causing the signal lines to discharge charges accumulated in the radiation detection element when an on-voltage is applied;
A readout circuit that converts the electric charge emitted from the radiation detection element into image data and reads the image data;
Prior to radiographic image capture, the scanning drive means sequentially applies an on-voltage to each scanning line to cause the irradiation start detection data to be read, and radiation irradiation is performed based on the read irradiation start detection data. Control means for detecting that it has started;
With
The control means includes
When the start of radiation irradiation is detected, an off voltage is applied to each scanning line from the scanning driving unit, and after passing through a charge accumulation state in which each switching unit is turned off, at least the scanning driving unit and the readout circuit are After performing control and reading processing of image data from the radiation detection element,
At the same time as the transmission processing for transmitting the preview image data based on the read image data to the console is started, the irradiation start detection data read processing is turned on for each scanning line of the detection unit from the scanning driving means. Apply voltage one by one in sequence,
Thereafter, in a state where no radiation is applied, an off voltage is applied to each scanning line from the scanning drive means for the same time as the charge accumulation state before the image data read processing, thereby turning off the switch means. Continue the charge accumulation state,
If the transmission processing of the preview image data is not completed when the continuation of the charge accumulation state is completed, the transmission processing is stopped and then the offset data reading processing is performed.

Furthermore, the radiographic imaging system of the present invention includes:
The radiographic imaging device of the present invention comprising a communication means;
A console that generates a preview image based on the data for the preview image transmitted from the radiation image capturing apparatus and displays the preview image on the display unit;
With
The console generates the preview image based on the preview image data each time the preview image data is transmitted from the radiographic imaging device, and reads the preview image data. The generated preview image is displayed at a position on the display unit corresponding to a position on the detection unit of the radiographic image capturing device of the radiation detection element thus formed, and the preview image is displayed on the display unit. It is characterized in that a wipe is displayed on the top.

  According to the radiographic image capturing apparatus and radiographic image capturing system of the system of the present invention, the radiation image capturing apparatus starts radiation irradiation based on the leak data dleak and the irradiation start detection data d read before capturing the radiation image. Is accurately detected.

  Therefore, even when the interface between the radiographic imaging device and the radiation generating device cannot be constructed (or the interface is not constructed), the radiographic imaging device itself accurately detects the start of radiation irradiation, and the radiographic image Shooting can be performed appropriately.

  Further, in the radiographic image capturing apparatus, not only during one detection operation after the reading process of the image data D as the main image, but also during the period including the period during which the charge accumulation state continues thereafter, Send the data to the console. Then, the console displays a preview image based on the transmitted preview image data.

  Therefore, even if the data for all the preview images cannot be transmitted to the console during one detection operation after the read processing of the image data D or during the subsequent charge accumulation state, one detection operation is performed. It is possible to transmit a considerable amount of preview image data to the console from the radiographic image capturing apparatus during the time when the image is stored and the duration of the charge accumulation state.

  For this reason, even if all the preview images cannot be displayed on the console, for example, as shown in FIG. 30 to be described later, whether the radiographer appropriately captures the subject in the image or whether re-imaging is necessary, etc. It is possible to display a preview image to such an extent that the above determination can be made with sufficient accuracy. Therefore, if the radiologist looks at the preview image displayed on the console, at least the necessity of re-imaging can be determined with sufficient accuracy.

  In addition, according to the radiographic image capturing apparatus and radiographic image capturing system of the system of the present invention, the reading of the image data D as the main image is performed regardless of whether the transmission process of the preview image data is completed or not. After the processing, the offset data O reading process is immediately started when one detection operation and the continuation of the charge accumulation state are completed.

  Therefore, as in the case of a conventional apparatus or system, after the read processing of the image data D as the main image, the reset processing of each radiation detection element 7 is repeated until the transmission processing of the preview image data is completed, and thereafter Compared with the case where it is configured to shift to the charge accumulation state, it is possible to start the reading process of the offset data O and transmit each data to the console at an early stage, and to perform one radiographic imaging in a short time. It becomes possible.

It is a perspective view which shows the external appearance of the radiographic imaging apparatus which concerns on this embodiment. It is sectional drawing which follows the XX line in FIG. It is a perspective view showing the state which connected the connector of the cable to the connector of the radiographic imaging apparatus. It is a top view which shows the structure of the board | substrate of a radiographic imaging apparatus. 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 a side view explaining the board | substrate with which a flexible circuit board, a PCB board | substrate, etc. were attached. It is a block diagram showing the equivalent circuit of a radiographic imaging apparatus. It is a block diagram showing the equivalent circuit about 1 pixel which comprises a detection part. It is a timing chart showing the ON / OFF timing of the charge reset switch and TFT in the reset processing of each radiation detection element. 6 is a timing chart showing charge reset switches, pulse signals, and TFT on / off timings in image data read processing. It is a figure which shows the structural example of the radiographic imaging system which concerns on this embodiment constructed | assembled in the imaging | photography room. It is a figure which shows the structural example of the radiographic imaging system which concerns on this embodiment constructed | assembled on the round-trip vehicle. It is a figure explaining that each electric charge which leaked from each radiation detection element via TFT is read as leak data. 6 is a timing chart showing on / off timings of charge reset switches and TFTs in a leak data read process. 6 is a timing chart showing charge reset switches, pulse signals, and on / off timings of TFTs in a case where leak data reading processing and radiation detection element reset processing are alternately performed before radiographic imaging. 6 is a timing chart for explaining the timing of applying an on-voltage to each scanning line in the detection method 1; It is a graph showing the example of the time transition of the leak data read. 6 is a timing chart showing the timing of sequentially applying an ON voltage to each scanning line when image data reading processing is repeatedly performed before radiographic image capturing in Detection Method 2; 6 is a timing chart showing a charge reset switch, a pulse signal, TFT on / off timing, and on time ΔT in image data read processing before radiographic imaging. 6 is a timing chart for explaining the timing of applying an ON voltage to each scanning line in the detection method 2. It is a figure showing the state by which the detection part was divided | segmented into four area | regions and read-out IC was each allocated to each area | region. It is a figure which shows the procedure of radiographic imaging, each process, etc. in the radiographic imaging apparatus and radiographic imaging system which concern on this embodiment. It is a timing chart explaining the timing etc. which apply an ON voltage to each scanning line when reset processing of each radiation detection element is performed in a normal short cycle. It is a figure which shows the procedure of radiographic imaging, each process, etc. in the conventional radiographic imaging apparatus and a radiographic imaging system. 6 is a timing chart for explaining the timing of applying an ON voltage to each scanning line in each processing from reading processing of image data as a main image to reading processing of offset data. FIG. 6 is a diagram illustrating a procedure and processes when the transmission process of the preview image data cannot be completed within the duration of the charge accumulation state in the radiographic imaging apparatus or radiographic imaging system according to the present embodiment. is there. It is a figure explaining an example of the method of extracting thinning-out data from image data. It is a figure showing the preview image etc. in the middle of being wipe-displayed on the display part of a console. It is a figure showing the preview image etc. after being wipe-displayed on the display part of a console. FIG. 27 is a diagram illustrating an example of a preview image displayed when the transmission process of preview image data cannot be completed within the duration of the charge accumulation state as illustrated in FIG. 26. It is an image figure showing extracting image data D sequentially, shifting the scanning line which extracts image data D from the center part of a detection part to a terminal part. It is the expanded image figure explaining the method of extraction of the thinning data in the extraction method 1-3. It is a figure explaining the preview image of (A) low resolution, (B) medium resolution, and (C) high resolution displayed on the display part of a console when the extraction method 1-3 is employ | adopted. It is a figure explaining the preview image of (A) low resolution, (B) medium resolution, and (C) high resolution displayed on the display part of a console when the extraction method 2-3 is employ | adopted.

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

  In the following description, a so-called indirect radiation image capturing apparatus that includes a scintillator or the like and converts an emitted radiation into an electromagnetic wave having another wavelength such as visible light to obtain an electrical signal will be described. The present invention can also be applied to a so-called direct type radiographic imaging apparatus that directly detects radiation with a radiation detection element without using a scintillator or the like.

  The present invention is applicable not only to the so-called portable radiographic image capturing apparatus described in the present embodiment, but also to a dedicated radiographic image capturing apparatus formed integrally with, for example, a support base. It is possible.

[Radiation imaging equipment]
FIG. 1 is a perspective view showing an external appearance of the radiographic image capturing apparatus according to the present embodiment, and FIG. 2 is a cross-sectional view taken along line XX of FIG. As shown in FIG. 1 and FIG. 2, the radiographic image capturing apparatus 1 houses a sensor panel SP including a scintillator 3, a substrate 4, and the like in a housing 2.

  In the present embodiment, a hollow rectangular tube-shaped housing body 2A having a radiation incident surface R in the housing 2 is formed of a material such as a carbon plate or plastic that transmits radiation. The housing 2 is formed by closing the openings on both sides of the portion 2A with the lid members 2B and 2C. Further, the lid member 2B on one side of the housing 2 has a power switch 37, a changeover switch 38, a connector 39, an indicator 40 composed of an LED or the like for displaying a battery state, an operating state of the radiographic imaging apparatus 1, and the like. Is arranged.

  In this embodiment, the connector 39 is connected to a connector C provided at the end of the cable Ca, for example, as shown in FIG. 3, for example, an external console 58 (see FIGS. 11 and 12 described later), etc. It functions as a wired communication means for transmitting and receiving signals and the like and transmitting image data D and the like to and from the above apparatus.

  Although not shown, for example, the antenna device 41 (see FIG. 7 to be described later) is provided in the lid member 2C on the opposite side of the housing 2, for example, by being embedded in the lid member 2C. Then, the antenna device 41 functions as a communication unit when transmitting and receiving a radio signal such as a signal between the radiographic imaging device 1 and the console 58 or the like.

  As shown in FIG. 2, a base 31 is disposed inside the housing 2 via a lead thin plate (not shown) on the lower side of the substrate 4, and an electronic component 32 and the like are disposed on the base 31. The PCB substrate 33, the battery 24, and the like are attached. Further, a glass substrate 34 for protecting the substrate 4 and the radiation incident surface R of the scintillator 3 is disposed. In the present embodiment, the buffer material 35 is provided between the sensor panel SP and the side surface of the housing 2.

  The scintillator 3 is provided at a position on the substrate 4 that faces a detection unit P described later. In the present embodiment, the scintillator 3 is, for example, a phosphor whose main component is converted into an electromagnetic wave having a wavelength of 300 to 800 nm, that is, an electromagnetic wave centered on visible light and output when receiving radiation. .

  Moreover, in this embodiment, the board | substrate 4 is comprised by the glass substrate, and as shown in FIG. 4, on the surface 4a by the side of the board | substrate 4 facing the scintillator 3, several scanning line 5 and several sheets are provided. The signal lines 6 are arranged so as to cross each other. A radiation detection element 7 is provided 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.

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

  When the radiation detection element 7 receives radiation from the radiation incident surface R of the housing 2 of the radiographic imaging apparatus 1 and is irradiated with electromagnetic waves such as visible light converted from the radiation by the scintillator 3, the radiation detection element 7 has electron positive inside. Generate hole pairs. In this way, the radiation detecting element 7 converts the irradiated radiation (electromagnetic wave converted from the radiation by the scintillator 3 in this embodiment) into electric charge.

  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. As shown in FIG. 5 which is an enlarged view of FIG. 4, each radiation detection element 7 is connected to a source electrode 8s of a TFT 8 which is a switch means. 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 gate electrode 8g via the scanning line 5 from the scanning driving means 15 described later, and is accumulated in the radiation detection element 7 via the source electrode 8s and the drain electrode 8d. The charged electric charge is discharged to the signal line 6. The TFT 8 is turned off when an off voltage is applied to the gate electrode 8g via the connected scanning line 5, and the emission of the charge from the radiation detecting element 7 to the signal line 6 is stopped, and the radiation detecting element The electric charge is accumulated in 7.

  In the present embodiment, as shown in FIG. 5, one bias line 9 is connected to a plurality of radiation detection elements 7 arranged in rows, and as shown in FIG. Each is arranged in parallel to the signal line 6. Further, each bias line 9 is bound to the connection 10 at a position outside the detection portion P of the substrate 4.

  As shown in FIG. 4, in this embodiment, 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.

  As shown in FIG. 6, each input / output terminal 11 has a flexible circuit board (Chip On Film) in which chips such as a readout IC 16 described later and a gate IC 15c constituting a gate driver 15b of the scanning drive means 15 are incorporated on a film. 12) are connected via an anisotropic conductive adhesive material 13 such as an anisotropic conductive adhesive film or an anisotropic conductive paste.

  The flexible circuit board 12 is routed to the back surface 4b side of the substrate 4 and is connected to the PCB substrate 33 described above on the back surface 4b side. In this way, the sensor panel SP of the radiation image capturing 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 a block diagram showing an equivalent circuit of the radiographic imaging apparatus 1 according to the present embodiment, and FIG. 8 is a block diagram showing an equivalent circuit for 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 7b, and each bias line 9 is bound to the connection 10 to the bias power source 14. It is connected. The bias power supply 14 applies a reverse bias voltage (that is, a voltage equal to or lower than the voltage applied to the first electrode 7 a side of the radiation detection element 7) to the second electrode 7 b of each radiation detection element 7 via the connection 10 and each bias line 9. It is designed to be applied.

  The scanning drive means 15 includes a power supply circuit 15a for supplying an on voltage and an off voltage to the gate driver 15b via the wiring 15d, and a voltage applied to each line L1 to Lx of the scanning line 5 between the on voltage and the off voltage. A gate driver 15b that switches between the on state and the off state of each TFT 8 is provided. In the present embodiment, the gate driver 15b includes a plurality of gate ICs 15c (see FIG. 6) arranged in parallel.

  As shown in FIGS. 7 and 8, each signal line 6 is connected to each readout circuit 17 built in the readout IC 16. The readout circuit 17 includes an amplification circuit 18 and a correlated double sampling circuit 19. An analog multiplexer 21 and an A / D converter 20 are further provided in the read IC 16. 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 a charge amplifier circuit including an operational amplifier 18a, a capacitor 18b and a charge reset switch 18c connected in parallel to the operational amplifier 18a, and a power supply unit 18d that supplies power to the operational amplifier 18a and the like. It consists of Further, the signal line 6 is connected to the inverting input terminal on the input side of the operational amplifier 18 a of the amplifier circuit 18, and the reference potential V ₀ is applied to the non-inverting input terminal on the input side of the amplifier circuit 18. ing.

  The charge reset switch 18 c of the amplifier circuit 18 is connected to the control means 22, and is turned on / off by the control means 22. Further, a switch 18e that opens and closes in conjunction with the charge reset switch 18c is provided between the operational amplifier 18a and the correlated double sampling circuit 19, and the switch 18e is turned on / off by the charge reset switch 18c. It is designed to be turned off / on in conjunction with

  When the radiation imaging apparatus 1 performs reset processing of each radiation detection element 7 for removing the charge remaining in each radiation detection element 7, as shown in FIG. 9, the charge reset switch 18c is turned on. Each TFT 8 is turned on in the state (and the switch 18e is turned off).

  Then, charges are emitted from the radiation detection elements 7 to the signal lines 6 through the TFTs 8 which are turned on, pass through the charge reset switch 18c of the amplifier circuit 18, and are supplied from the output terminal side of the operational amplifier 18a to the operational amplifier 18a. Passing through, it goes out from the non-inverting input terminal and is grounded or flows out to the power supply unit 18d. In this way, the reset processing of each radiation detection element 7 is performed.

  On the other hand, when the image data D is read from each radiation detection element 7, the charge reset switch 18c of the amplifier circuit 18 is turned off (and the switch 18e is turned on) as shown in FIG. In this state, when charges are released from the radiation detection elements 7 to the signal lines 6 through the TFTs 8 that are turned on, the charges are accumulated in the capacitor 18 b of the amplifier circuit 18.

  In the amplifier circuit 18, a voltage value corresponding to the amount of charge accumulated in the capacitor 18 b is output from the output side of the operational amplifier 18 a, and the charge flowing out from each radiation detection element 7 is charged by the amplifier circuit 18. The voltage is converted.

  The correlated double sampling circuit (CDS) 19 provided on the output side of the amplifier circuit 18 receives the pulse signal Sp1 (see FIG. 10) from the control means 22 before the electric charge flows out from each radiation detection element 7. Then, the voltage value Vin output from the amplifier circuit 18 at that time is held, and after the electric charge flowing out from each radiation detection element 7 is accumulated in the capacitor 18b of the amplifier circuit 18 as described above, the control means When the pulse signal Sp2 is transmitted from 22, the voltage value Vfi output from the amplifier circuit 18 at that time is held.

  The correlated double sampling circuit 19 calculates a difference Vfi−Vin between these voltage values, and outputs the calculated difference Vfi−Vin as analog value image data D to the downstream side. The image data D of each radiation detection element 7 output from the correlated double sampling circuit 19 is sequentially transmitted to the A / D converter 20 via the analog multiplexer 21, and is sequentially digitalized by the A / D converter 20. The image data D is converted into value data, output to the storage means 23, and sequentially stored.

  The control means 22 includes a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), an input / output interface, etc., not shown, connected to a bus, an FPGA (Field Programmable Gate Array), or the like. It is configured. 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. Further, as shown in FIG. 7 and the like, the control means 22 is connected to a storage means 23 composed of SRAM (Static RAM), SDRAM (Synchronous DRAM) or the like.

  In the present embodiment, the antenna unit 41 described above is connected to the control unit 22, and each member such as the detection unit P, the scanning drive unit 15, the readout circuit 17, the storage unit 23, the bias power supply 14, and the like. A battery 24 for supplying electric power is connected. The battery 24 is provided with a connection terminal 25 for charging the battery 24 by supplying power to the battery 24 from a charging device (not shown).

  As described above, the control unit 22 controls the scanning drive unit 15 and the readout circuit 17 to perform the readout process of the image data D, the reset process of each radiation detection element 7, and the like. The operation of each functional unit is controlled.

  In the present embodiment, the radiographic image capturing apparatus 1 is configured to detect the start of radiation irradiation by the apparatus itself. The control configuration and the like for this purpose are the configuration of the radiographic image capturing system according to the present embodiment. This will be described after the description.

[Radiation imaging system]
Next, the radiographic image capturing system 50 according to the present embodiment will be described. FIG. 11 is a diagram illustrating a configuration example of the radiation image capturing system 50 according to the present embodiment. In FIG. 11, the case where the radiographic imaging system 50 is constructed in the imaging room R1 is shown.

  In the photographing room R1, a bucky device 51 is installed, and the bucky device 51 can be used by loading the radiographic imaging device 1 in its cassette holding part (also referred to as a cassette holder) 51a. It has become. FIG. 11 shows a case where a bucky device 51A for standing position shooting and a bucky device 51B for standing position shooting are installed as the bucky device 51. For example, only one of the bucky devices 51 is provided. It may be done.

  As shown in FIG. 11, at least one radiation source 52 </ b> A for irradiating the radiation image capturing apparatus 1 loaded in the Bucky apparatus 51 via the subject is provided in the imaging room R <b> 1. In the present embodiment, by moving the position of the radiation source 52A or changing the irradiation direction of the radiation, radiation is applied to both the standing-up imaging device 51A and the standing-up imaging device 51B. Can be done.

  The imaging room R1 is provided with a repeater (also referred to as a base station or the like) 54 for relaying communication between the devices in the imaging room R1 and the devices outside the imaging room R1. In the present embodiment, the repeater 54 is provided with a wireless antenna (also referred to as an access point) 53 so that the radiation image capturing apparatus 1 can transmit and receive image data D and signals in a wireless manner. It has been.

  The repeater 54 is connected to the radiation generator 55 and the console 58, and LAN (Local Area Network) communication is transmitted to the repeater 54 from the radiation imaging apparatus 1, the console 58, and the like to the radiation generator 55. A converter (not shown) that converts a signal for use into a signal for use in the radiation generator 55 and the reverse conversion is incorporated.

  In the present embodiment, the front room (also referred to as an operation room) R2 is provided with an operation console 57 of the radiation generating device 55. The operation panel 57 is operated by an operator such as a radiation engineer. An exposure switch 56 is provided for instructing the generator 55 to start radiation irradiation.

  The radiation generating device 55 moves the radiation source 52 to a predetermined position, adjusts the radiation direction thereof, and irradiates a predetermined area of the radiographic imaging device 1 with a diaphragm or a collimator (not shown). Etc., or various controls such as adjusting the radiation source 52 so that an appropriate dose of radiation is applied.

  As shown in FIG. 11, in the present embodiment, a console 58 formed of a computer or the like is provided in the front chamber R2. The console 58 can be configured to be provided outside the imaging room R1 and the front room R2, in a separate room, and the like, and is installed in an appropriate place.

  Further, the console 58 is provided with a display unit 58a configured to include a CRT (Cathode Ray Tube), an LCD (Liquid Crystal Display), and the like, and also includes input means such as a mouse and a keyboard (not shown). Yes. In addition, the console 58 is connected to or has a built-in storage means 59 composed of an HDD (Hard Disk Drive) or the like.

  On the other hand, as shown in FIG. 12, the radiographic image capturing apparatus 1 can be used in a so-called state without being loaded into the bucky device 51. For example, when the patient H cannot get up from the bed B of the patient room R3 and cannot go to the imaging room R1, the radiographic imaging device 1 is brought into the patient room R3 as shown in FIG. It can be used by being inserted into the patient's body or applied to the patient's body.

  When the radiographic image capturing apparatus 1 is used in a hospital room R3 or the like, instead of the radiation generating apparatus 55 installed in the above-described imaging room R1, as shown in FIG. It is brought into hospital room R3 by being mounted on 71 or the like. In this case, the radiation 52P of the portable radiation generator 55 is configured to be able to emit radiation in an arbitrary direction, and is inserted between the bed B and the patient's body or applied to the patient's body. The radiation image capturing apparatus 1 can be irradiated with radiation from an appropriate distance and direction.

  Further, in this case, a repeater 54 provided with a wireless antenna 53 is built in the radiation generation device 55, and, similarly to the above, the repeater 54 communicates between the radiation generation device 55 and the console 58, The communication between the radiation image capturing apparatus 1 and the console 58, the transmission of image data D, and the like are relayed.

  In addition, as shown in FIG. 11, the radiographic imaging device 1 is inserted between the patient's body lying on the bucky device 51B for supine photography in the photographing room R1 and the bucky device 51B for supine photography. It can also be used by being applied to the patient's body on the bucky device 51B for photographing from the upright position. In this case, either the portable radiation 52P or the radiation source 52A installed in the photographing room R1 is used. It is also possible to use it.

  In this embodiment, as will be described later, when the thinning data Dt is transmitted from the radiographic image capturing apparatus 1 as preview image data, the console 58 displays the preview image p_pre every time the thinning data Dt is transmitted. This is generated and displayed on the display unit 58a as a wipe. This will be described later.

  Further, as will be described later, when the remaining image data D and the like are subsequently transmitted from the radiation image capturing apparatus 1, the console 58 restores the original all image data D from the thinned data Dt and the remaining image data D. The final radiation image p is generated by performing precise image processing such as gain correction, offset correction, defective pixel correction, and gradation processing according to the imaging region based on the offset data O and the like. ing.

[Control configuration of detection of radiation irradiation start in radiographic imaging device]
Next, the control configuration of the radiation irradiation start detection process in the radiographic imaging device 1 configured as described above will be described.

  In the present embodiment, as described above, the radiation image capturing apparatus 1 itself detects that radiation has been emitted from the radiation source 52 (see FIGS. 11 and 12) of the radiation generation apparatus 55. Hereinafter, a method of detecting the start of radiation irradiation performed by the radiation image capturing apparatus 1 according to the present embodiment will be described.

  Note that the detection method according to the present embodiment is a detection method newly found by the inventors' research, and as described in Patent Document 4 and Patent Document 5 described above, a current is generated in the apparatus. A method of providing a detection unit and detecting the start of radiation irradiation based on an output value from the current detection unit is not employed.

  As a detection method newly found by the inventors' research, for example, either of the following two detection methods can be employed.

[Detection method 1]
For example, before the radiation image capturing apparatus 1 is irradiated with radiation in the radiation image capturing, it is possible to repeatedly perform the reading process of the leak data dleak. Here, as shown in FIG. 13, the leakage data dleak is a charge q leaked from each radiation detection element 7 via each TFT 8 which is in an off state in a state where an off voltage is applied to each scanning line 5. This data corresponds to the total value for each signal line 6.

  In the readout process of the leak data dleak, unlike the reset process of each radiation detection element 7 shown in FIG. 9 and the readout process of the image data D shown in FIG. 10, as shown in FIG. A pulse is applied from the control means 22 to the correlated double sampling circuit 19 of each readout circuit 17 (see CDS in FIG. 7 and FIG. 8) in a state where the TFT 8 is turned off by applying an off voltage to each of the lines L1 to Lx. Signals Sp1 and Sp2 are transmitted.

  When the pulse signal Sp <b> 1 is transmitted from the control unit 22, the correlated double sampling circuit 19 holds the voltage value Vin output from the amplifier circuit 18 at that time. Then, the charge q leaked from each radiation detection element 7 via each TFT 8 is accumulated in the capacitor 18b of the amplifier circuit 18 to increase the voltage value output from the amplifier circuit 18, and the pulse signal Sp2 is transmitted from the control means 22. Then, the correlated double sampling circuit 19 holds the voltage value Vfi output from the amplifier circuit 18 at that time.

  And the value which the correlated double sampling circuit 19 calculated and output the difference Vfi−Vin of the voltage value becomes the leak data dleak. The leak data dleak is then converted into a digital value by the A / D converter 20 as in the case of the image data D reading process described above.

  By the way, if only the reading process of the leak data dleak is repeatedly performed, each TFT 8 remains in an OFF state, and dark charges generated in each radiation detection element 7 are accumulated in each radiation detection element 7. It will be in a state to continue.

  Therefore, as described above, in the case where the readout process of the leak data dleak is repeatedly performed before radiographic imaging, the off-voltage is applied to each scanning line 5 as shown in FIG. It is desirable that the reading process of the leak data dleak and the reset process of the radiation detecting elements 7 performed by sequentially applying the ON voltage to the lines L1 to Lx of the scanning line 5 are alternately repeated. Note that T, τ, and Tac in FIG. 15 and FIG. 16 to be described later will be described later.

  In this way, when the readout process of the leak data dleak and the reset process of each radiation detection element 7 are alternately performed before radiographic imaging, when radiation irradiation to the radiographic imaging apparatus 1 is started. Electromagnetic waves converted from radiation by the scintillator 3 (see FIG. 2) are irradiated to each TFT 8. As a result, the inventors have found that the charge q (see FIG. 15) leaked from each radiation detection element 7 via each TFT 8 increases.

  For example, as shown in FIG. 16, when the readout process of the leak data dleak and the reset process of each radiation detection element 7 are alternately repeated before radiographic imaging, as shown in FIG. 17, the radiographic imaging apparatus The leak data dleak read at the time when the irradiation of the radiation to 1 is started becomes a value significantly larger than the leak data dleak read before that.

  16 and 17, the leak data dleak read in the fourth read process after the on-voltage is applied to the line L4 of the scanning line 5 in FIG. 16 and the reset process is performed is shown in FIG. Corresponds to the leak data dleak at time t1. In FIG. 16, “R” represents a reset process for each radiation detection element 7, and “L” represents a read process for leak data dleak.

  Therefore, the control means 22 of the radiographic image capturing apparatus 1 is configured to monitor the leak data dleak read out in the read processing of the leak data dleak before radiographic image capture, and the read out leak data dleak is, for example, It can be configured to detect that irradiation of radiation has started when a predetermined threshold value dleak_th (see FIG. 17) set in advance is exceeded. Processing subsequent to the detection processing of the start of radiation irradiation will be described later.

[Detection method 2]
Further, as shown in FIG. 18, instead of the configuration in which the leak data dleak is read out before radiographic imaging as in the detection method 1 described above, the gate of the scanning drive unit 15 is configured as shown in FIG. 18 before radiographic imaging. It is also possible to apply a turn-on voltage sequentially to each line L1 to Lx of the scanning line 5 from the driver 15b and to repeatedly read out the image data d from each radiation detection element 7.

  In addition, as described above, the image data d read out for detection of the start of radiation irradiation before the radiographic image capture is hereinafter referred to as image data D as the main image performed immediately after the image capture. This is called detection data d.

  Further, in the reading process of the irradiation start detection data d, on / off of the charge reset switch 18c of the amplifier circuit 18 of the read circuit 17, transmission of the pulse signals Sp1 and Sp2 to the correlated double sampling circuit 19, etc. are shown in FIG. As shown in FIG. 19, the processing is performed in the same manner as the processing of reading out the image data D shown in FIG. Note that T and ΔT in FIG. 19 and the like will be described later.

  When the irradiation start detection data d is read out before radiographic imaging as described above, when radiation irradiation is started on the radiographic imaging apparatus 1 as shown in FIG. The irradiation start detection data d read in (1) (the irradiation start detection data d read out by applying an ON voltage to the line Ln of the scanning line 5 in FIG. 20) is the leak data shown in FIG. As in the case of dleak, the value is much larger than the irradiation start detection data d read before that.

  Therefore, the control means 22 of the radiographic image capturing apparatus 1 is configured to monitor the irradiation start detection data d read in the read processing before radiographic image capturing, and the read irradiation start detection data d is It can be configured to detect that radiation irradiation has started when a predetermined threshold value dth is exceeded. Note that ΔT, τ, and Tac in FIG. 20 will be described below.

[About processing to improve detection sensitivity]
Further, in the detection method 1 described above, the application of the on-voltage to the next scanning line 5 is started after the application of the on-voltage to a certain scanning line 5 is started in the reset process of each radiation detection element 7 before radiographic image capturing The period τ (see FIG. 15, FIG. 16, etc.) until the transmission is lengthened, and the transmission interval T of the two pulse signals Sp1 and Sp2 transmitted from the control means 22 in the reading process of the leak data dleak is lengthened. Is possible.

  With this configuration, the value of the leak data dleak read in one read process of the leak data dleak increases. Therefore, the detection sensitivity at the start of radiation irradiation in the radiographic imaging apparatus 1 is improved.

  In the detection method 2 described above, in the reading process of the irradiation start detection data d before radiographic image capturing, the time ΔT (see FIGS. 19 and 20) for turning on each TFT 8, that is, the gate of the scanning drive unit 15. It is possible to increase the time ΔT (hereinafter referred to as “on time ΔT”) from when the driver 15 b applies the on-voltage to the scanning line 5 until the driver 15 b switches to the off-voltage.

  If comprised in this way, the value of the irradiation start detection data d read by the read-out process of the irradiation start detection data d of 1 time will become large. Therefore, the detection sensitivity at the start of radiation irradiation in the radiographic imaging apparatus 1 is also improved.

  In this case as well, the period τ (see FIG. 20) from the start of application of the on-voltage to a certain scan line 5 to the start of application of the on-voltage to the next scan line 5 or transmission from the control means 22 The transmission interval T (see FIG. 19) of the two pulse signals Sp1 and Sp2 becomes longer.

  As described above, when the detection method 1 or the detection method 2 described above is employed, in order to improve the detection sensitivity at the start of radiation irradiation in the radiographic imaging apparatus 1, the radiation detection elements 7 before the radiographic imaging are detected. The above-described period τ in the reset process and the irradiation start detection data d read process, the process of increasing the transmission interval T of the two pulse signals Sp1 and Sp2 transmitted from the control means 22, or the on-time ΔT are appropriately performed. Done.

[Improved detection method of radiation start]
Incidentally, several thousand to several tens of thousands of signal lines 6 are usually wired in the detection unit P (see FIGS. 4 and 7, etc.) of the radiographic image capturing apparatus 1, and a readout circuit is connected to each signal line 6. 17 is provided. Therefore, the leak data dleak and the irradiation start detection read out by one reading process of the leakage data dleak (in the case of the detection method 1 described above) and the reading processing of the irradiation start detection data d (in the case of the detection method 2 described above). The number of data d ranges from thousands to tens of thousands.

  If the processing for determining whether or not the threshold value dleak_th or the like is exceeded for each of the leak data dleak or the like as described above is performed for each read process, the burden on the detection process becomes very heavy. There is a possibility that the start of radiation irradiation cannot be detected in real time.

  Therefore, for example, in the present embodiment, 128 or 256 read circuits 17 (see FIG. 7 or the like) are built in the read IC 16 to use the read IC 16 once for each read IC 16. In the readout process, a statistical value dleak_st (z) (z is the number of the readout IC 16) such as an average value of leak data dleak read out from a predetermined number of readout circuits 17 incorporated in the readout IC 16 is calculated. It is possible to configure.

  With this configuration, for example, 8192 signal lines 6 are provided on the detection unit P, and 256 readout circuits 17 are built in one readout IC 16 (that is, 256 in one readout IC 16). Assuming that two signal lines 6 are connected), the total number of read ICs 16 is 8192 ÷ 256 = 32.

  Therefore, the control means 22 of the radiographic image capturing apparatus 1 does not determine whether, for example, 8192 pieces of leak data dleak read out in one reading process have exceeded the threshold value dleak_th, respectively, 32 pieces of leak data. It can be configured to determine whether or not the statistical value dleak_st (z) of dleak exceeds a threshold value.

  Therefore, there is a merit that the burden on the determination process of the start of radiation irradiation in the control means 22 of the radiographic imaging apparatus 1 is reduced, and the start of radiation irradiation can be accurately detected in real time.

  Further, various improvements can be added to the detection method 1 and the detection method 2 in order to reduce the burden on the detection process of the start of radiation irradiation. Then, various values are calculated from the read leak data dleak and irradiation start detection data d by various improved methods, and the radiation irradiation start detection process is performed based on the calculated values. In addition, it is possible to quickly detect the start of radiation irradiation.

  Furthermore, for example, when the detection unit P (see FIGS. 4 and 7) of the radiographic imaging device 1 is divided into a plurality of regions Pa to Pd as shown in FIG. It is also possible to configure the control means 22 to detect the start of radiation irradiation on the radiographic imaging device 1 when the start of irradiation is detected.

[Procedure for radiographic imaging in the present invention]
Next, procedures and processes of radiographic imaging in the radiographic imaging apparatus 1 and the radiographic imaging system 50 according to the present embodiment will be described with reference to FIGS. The operation of the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to the present embodiment will also be described.

  In the following description, mainly the detection method 1 described above, that is, the leakage data dleak reading process and the resetting process of each radiation detection element 7 are alternately performed before radiographic imaging, and calculation is performed based on the read leakage data dleak and the read data. Although the case where the start of radiation irradiation is detected based on each of the values will be described, the same applies to the case where the above detection method 2 is employed.

[Reset processing of each radiation detection element]
In the present embodiment, as shown in FIG. 22, for example, when a signal to start radiographic imaging is transmitted from the console 58 to the radiographic imaging apparatus 1, the control unit 22 of the radiographic imaging apparatus 1 First, the reset processing of each radiation detection element 7 for removing the extra charge remaining in each radiation detection element 7 from each radiation detection element 7 is performed.

  The reset process in this case is not a so-called long-period reset process in which the cycle τ (see FIG. 15 and FIG. 16 and the like) alternately performed with the read-out process of the leak data dleak before radiographic imaging described above is long, but is not shown in FIG. As shown in FIG. 5, the so-called normal short cycle resetting process in which the cycle τ for sequentially applying the ON voltage from the gate driver 15b of the scanning driving unit 15 to the lines L1 to Lx of the scanning line 5 is short is repeated a predetermined number of times. It has come to be.

  In this case, an on-voltage is sequentially applied from the gate driver 15b to the lines L1 to Lx of the scanning line 5, and an on-voltage is applied to each scanning line 5 provided in the detection unit P once to perform a reset process. The case where it is performed is one reset process. In the case of FIG. 23, four reset processes are described. And as said predetermined frequency | count, appropriate frequency | counts, such as 1 time, 5 times, 10 times, are set.

[Detection of radiation irradiation start]
When the control unit 22 of the radiation image capturing apparatus 1 finishes the reset process of each radiation detection element 7, the control unit 22 then proceeds to a process for detecting the start of radiation irradiation. The detection process of the start of radiation irradiation is performed according to the method described above.

  In particular, when the detection method 1 described above is used to detect the start of radiation irradiation, the detection process for one time immediately after the transition from the reset process to the detection process is performed ( See Fig. 22. That is, the above-described long-cycle reset process (see Figs. 15 and 16) alternately performed with the leak data dleak read process is applied to the lines L1 to Lx of the scanning line 5 once. The control means 22 does not perform the process for detecting the start of radiation irradiation.

  The reason for this configuration is as follows. In addition, when the same phenomenon appears in the read-out irradiation start detection data d when the detection method 2 is adopted, similarly, even when the detection method 2 is adopted, the reset process of each radiation detection element 7 is similarly performed. While performing one detection process immediately after shifting to the detection process, it is configured not to perform the radiation irradiation start detection process.

  In the study by the present inventors, when the process of resetting each radiation detection element 7 is shifted from the reset process to the detection process and the read process of the leak data dleak is performed, the read process of the leak data dleak is started immediately after the reset process is completed. It has been found that the value of leak data dleak read out immediately afterwards may increase.

  Although the cause of such a phenomenon is not necessarily clearly understood, as one cause, when the reset processing of each radiation detection element 7 is performed, the charge is released from each radiation detection element 7 to the signal line 6. In addition, a relatively large amount of charge is trapped in the trap level in each TFT 8. As described above, in the initial stage of reading the leak data dleak with each TFT 8 turned off, the charge trapped in the trap level of each TFT 8 leaks from the radiation detection element 7 to the signal line 6 via the TFT 8. Therefore, it is considered that the value of leak data dleak increases.

  Even if the leak data dleak immediately after the start of the reading process of the leak data dleak becomes large as described above, the value of the read leak data dleak converges to a normal relatively small value as the reading process is repeated. To do.

  When such a phenomenon occurs, if the detection process is performed immediately after the transition from the reset process of each radiation detection element 7 to the detection process, the leak data dleak having a large value immediately after the start of the read process or based on it. Each value calculated in this way exceeds the threshold value, and there is a possibility that it is erroneously detected that the radiation imaging apparatus 1 has started irradiation with radiation.

  Therefore, in the present embodiment, the control unit 22 of the radiographic imaging device 1 performs the detection process for one time immediately after the transition from the reset process of each radiation detection element 7 to the detection process of the start of radiation irradiation, as described above. While performing, the radiation irradiation start detection process (that is, the read leak data dleak and the process of comparing each value calculated based on the leak data dleak) is not performed.

  In the present embodiment, the value of the leaked data dleak that is read out converges to a normal relatively small value during one detection process. Therefore, during one detection process immediately after the transition to the detection process. However, if the convergence of the leak data dleak is prolonged, the number of times that the detection process is not performed may be increased.

  Further, since the leak data dleak read immediately after the transition from the reset process of each radiation detection element 7 to the detection process does not become a large value as described above, the leak data dleak having a relatively small value is read from the beginning. If there is, it is possible to perform the detection process of the start of radiation irradiation (that is, the process of comparing the read leak data dleak and each value calculated based on the threshold value) immediately after shifting to the detection process. .

  In the present embodiment, as shown in FIG. 22, the control means 22 of the radiographic image capturing apparatus 1 thereafter proceeds to the detection process of the start of radiation irradiation as described above, and the radiation irradiation is started. It is supposed to shift to a state waiting for.

[Transition to charge accumulation state]
Next, when the control means 22 of the radiographic image capturing apparatus 1 detects the start of radiation irradiation as described above, it shifts to a charge accumulation state as shown in FIG. .

  That is, as shown in FIG. 16 (in the case of the detection method 1) and FIG. 20 (in the case of the detection method 2), the application of the on-voltage to each scanning line 5 is stopped when the start of radiation irradiation is detected. Then, an off voltage is applied from the gate driver 15b to all the lines L1 to Lx of the scanning line 5, each TFT 8 is turned off, and the charge generated in each radiation detecting element 7 due to the irradiation of the radiation is transferred to each radiation detecting element 7. The state is shifted to a charge storage state to be stored inside.

[Reading process of image data D as main image]
For example, when a predetermined time has elapsed since the start of radiation irradiation was detected, the control unit 22 of the radiographic image capturing apparatus 1 performs a process of reading image data D as a main image as shown in FIG. It comes to let you.

  That is, in the present embodiment, the control unit 22 scans the scanning line to which the on-voltage is applied in the reset process immediately before the start of radiation irradiation detected in the read process of the leak data dleak before the radiographic image capturing. 5 (in the case of FIG. 16, the line L4 of the scanning line 5; hereinafter, generally referred to as a detection line), the scanning line 5 to which the ON voltage is to be applied (the line L5 of the scanning line 5 in the case of FIG. 16). The application of an on-voltage is started from a generalized reading start line), and an on-voltage is sequentially applied to each scanning line 5 to read out image data D as a main image.

  Similarly, in the case of the detection method 2, as shown in FIG. 20, when a predetermined time elapses after the control unit 22 detects the start of radiation irradiation, the control unit 22 stores the irradiation start detection data d before radiographic image capturing. The on-voltage is applied next to the scanning line 5 (that is, the detection line; in FIG. 20, the line Ln of the scanning line 5) to which the on-voltage is applied when it is detected that radiation irradiation has been started in the reading process. The application of the on-voltage starts from the scanning line 5 to be performed (that is, the readout start line; in the case of FIG. 20, the line Ln + 1 of the scanning line 5). The image data D is read out.

  In FIG. 16 and FIG. 20, when the read start line is the detection lines L4 and Ln + 1 of the scanning line 5, the application of the on-voltage is started from the read lines L5 and Ln + 1. Thus, the case where the reading process of the image data D as the main image is performed has been described. However, for example, the first line L1 of the scanning line 5 may be configured to be the reading start line.

  In the present embodiment, when the image data D as the main image is read out, the cycle in which the on-voltage is applied from the gate driver 15b to each scanning line 5 is the same as the reading processing of the leak data dleak before the radiographic imaging. Same as the period τ in the reset process (in the case of the detection method 1; see FIG. 16 and the like) and the reading process d of the irradiation start detection data d (in the case of the detection method 2 and see FIG. 20) which are alternately performed. An ON voltage is sequentially applied to each scanning line 5 so as to have a period.

[About each process after the reading process of the image data D]
When the reading process of the image data D as the main image is completed as described above, in the present embodiment, the control unit 22 of the radiographic image capturing apparatus 1 performs a preview based on the read image data D as shown in FIG. The transmission processing for transmitting image data to the console 58 and the detection operation for starting radiation irradiation are started simultaneously, and these processing and operations are performed in parallel.

[Detection operation after image data D is read out]
When the reading process of the image data D as the main image is completed as described above, as described above, conventionally, as shown in FIG. 24, until the transmission process of the preview image data to the console 58 is completed. For example, the reset processing of each radiation detection element 7 with a short period as shown in FIG. 23 is repeatedly performed.

  Then, after the transmission process is completed and the reset process of each radiation detection element 7 is completed, the transition to the charge accumulation state and the reading process of the offset data O are performed. However, with this configuration, there is a problem that the time required for the transmission process may become longer depending on, for example, the degree of congestion of the communication line, and the time required for one radiographic image may be longer. It was.

  Therefore, in the present embodiment, as shown in FIG. 22, the radiation irradiation start detection operation started simultaneously with the preview image data transmission processing is performed only once.

  That is, in this embodiment, when the above-described detection method 1 is employed, for example, the control unit 22 continues to leak data when the reading process of the image data D as the main image is completed as shown in FIG. The reset process of each radiation detection element 7 which is alternately performed with the readout process of the leak is transferred from the gate driver 15b (see FIG. 7 and the like) of the scanning drive unit 15 to the lines L5 to Lx and L1 to L4 of the scanning line 5 of the detection unit P Each of the ON voltages is sequentially applied once to perform the leak data dleak read processing (see L in FIG. 25) and reset processing of each radiation detection element 7 (see R in FIG. 25). It is designed to be performed alternately.

  At this time, the radiation image capturing apparatus 1 is not irradiated with radiation. For this reason, it is not necessary to perform the operation of detecting the start of radiation irradiation at this point, that is, before the offset data O reading process. However, in the present embodiment, as described above, when the reading process of the image data D as the main image is completed, the operation for detecting the start of radiation irradiation is performed. The reason for this will be briefly described below.

  In the radiographic imaging apparatus 1 having the above-described configuration, the cause is not necessarily clear, but when each radiation detection element 7 is reset, each readout circuit 17 is operated to leak data leak or irradiation start detection data. It is known that the potential of each signal line 6 changes between when data such as d is being read out.

  Then, immediately before shifting to the charge accumulation state before the offset data O reading process (see FIG. 25), each reading circuit 17 was operated to read leakage data dleak or the like, or each reading circuit 17 was operated. Depending on whether or not only the reset processing of each radiation detection element 7 is repeatedly performed, the potential of each signal line 6 at the time when each TFT 8 is turned off when shifting to the charge accumulation state becomes different.

  However, if the potential of the signal line 6 at the moment when each TFT 8 is switched from the on state to the off state changes, the potential difference between the TFT 8 and the signal line 6 changes, so that the exchange between the TFT 8 and the signal line 6 occurs. The amount of charge generated will be different. Therefore, the amount of residual charges existing in each radiation detection element 7 becomes different at the moment when each TFT 8 is switched from the on state to the off state.

  In the present embodiment, for example, when the above-described detection method 1 is adopted, as described above, the leakage data dleak and the reset processing of each radiation detection element 7 are alternately performed before radiographic imaging. After each TFT 8 is turned off and shifts to the charge accumulation state, a reading process of the image data D as the main image is performed (see FIG. 16 and the like).

  As can be seen from the above reason, the potential of the signal line 6 at the moment when each TFT 8 is switched from the ON state to the OFF state before the offset data O reading process is set, and the TFT 8 is set before the image data D reading process. Unless the potential is the same as the potential of the signal line 6 at the moment of switching from the on state to the off state, the amount of residual charges in each radiation detection element 7 at the time of the offset data O read processing is the amount of the image data D as the main image. The amount of charge remaining in each radiation detection element 7 at the time of readout processing is different.

  However, conversely, the potential of the signal line 6 at the moment when each TFT 8 is switched from the on state to the off state before the offset data O reading process, and the TFT 8 from the on state to the off state before the image data D reading process described above. If the potential is the same as the potential of the signal line 6 at the moment of switching to, the amount of residual charge in each radiation detection element 7 at the time of offset data O readout processing is the same as that at the time of readout processing of image data D as the main image. The amount is the same as the amount of residual charge in the radiation detection element 7.

  The offset data O read by the offset data O reading process is data having the same size as the offset due to the residual charges in each radiation detection element 7 superimposed on the image data D as the main image. . Therefore, in the subsequent image processing in the console 58, by subtracting the offset data O from the image data D, it is possible to accurately offset at least the offset due to the residual charge in each radiation detection element 7 in each data. It becomes possible.

  Before the offset data O reading process, the potential of the signal line 6 at the moment when each TFT 8 is switched from the ON state to the OFF state is the signal at the moment when each TFT 8 is switched from the ON state to the OFF state before the image data D reading process. In order to obtain the same potential as the potential of the line 6, the processing state before the reading process of the image data D as the main image may be reproduced before the reading process of the offset data O.

  Therefore, in the present embodiment, as described above, the leakage data dleak read processing and the reset processing of each radiation detection element 7 alternately performed before radiographic image capturing are performed after the image data D read processing as the main image. It is configured to be performed only once again.

  Note that the reading process of the leak data dleak and the irradiation start detection data d in this case is a process performed to make the potential of the signal line 6 the same as described above, and is based on the read leak data dleak and the like. Therefore, it is not necessary to perform the process of detecting the start of radiation irradiation.

  Therefore, in the present embodiment, the control unit 22 of the radiographic imaging apparatus 1 causes the readout circuit 17 and the like to read out the leak data dleak and the like, but compares the read out leak data dleak and the like with the threshold dleak_th and the like. The process, that is, the detection process of the start of radiation irradiation is not performed. In this sense, in the above description of each process after the reading process of the image data D as the main image, the description was made using the term “detection operation” instead of the detection process.

  In the present embodiment, the reason why the above-described reading process and resetting process of each radiation detection element 7 are performed by applying the on-voltage once for each scanning line 5 on the detection unit P is as follows. This is because a series of processes (that is, processes up to the offset data O reading process) can be performed in a shorter time.

  Further, as in the present embodiment, one of the reasons for performing the reading process of the leak data dleak and the like after the reading process of the image data D as the main image and before the reading process of the offset data O is as described above. As described above, in the radiographic image capturing apparatus 1 described above, the potential of each signal line 6 is different between when the radiation detection element 7 is reset and when the readout process is performed.

  Therefore, for example, in the radiographic imaging device, the potential of each signal line 6 is different between when the radiation detection element 7 is reset and when the readout circuit 17 is activated to perform the readout process. If the potentials are the same, it is necessary to perform a reading process such as leak data dleak after the reading process of the image data D as the main image and before the reading process of the offset data O as in the present embodiment. Absent.

  Therefore, in such a radiographic imaging apparatus, when the above-described detection method 1 is adopted, the readout of the leak data dleak is not performed in each readout circuit 17, and the leak data dleak before radiographic imaging is alternately performed. It is possible to configure so that only the reset process of each radiation detection element 7 is performed at the same period τ as the reset process of each radiation detection element 7 performed in the above.

  In addition, when the above-described detection method 2 is adopted, the same process is performed as the readout process of the irradiation start detection data d performed before the radiographic imaging after the readout process of the image data D as the main image. It is configured to repeat only once.

  However, at that time, the potential of each signal line 6 is different between the case where the radiographic imaging apparatus performs reset processing of each radiation detection element 7 and the case where readout processing is performed by operating each readout circuit 17. If the potentials are the same, instead of causing each readout circuit 17 to read out the irradiation start detection data d after the readout processing of the image data D as the main image, each scanning line 5 is turned on at the same cycle. It is possible to configure so that the radiation detection elements 7 are reset by sequentially applying voltages.

[Transition to charge accumulation state]
In the present embodiment, the control unit 22 of the radiographic image capturing apparatus 1 performs the radiation irradiation start detection operation only once after the reading process of the image data D as the main image as described above. In a state where no radiation is irradiated, as shown in FIG. 22 and FIG. 25, an off voltage is applied to each scanning line 5 from the gate driver 15b to shift to a charge accumulation state.

  In this case, as shown in FIG. 22, when one detection operation is completed regardless of whether or not transmission processing of preview image data from the radiation image capturing apparatus 1 to the console 58 described later is completed. It is configured to immediately shift to the charge accumulation state.

  In this embodiment, in the charge accumulation state in this case, each scanning line 5 is supplied from the gate driver 15b for the same time as the charge accumulation state (see FIGS. 16 and 20) before the read processing of the image data D as the main image. A charge accumulation state in which each TFT 8 is turned off by applying an off voltage to the TFT is continued.

[Send preview image data and display preview image]
On the other hand, in the present embodiment, as described above, the control unit 22 of the radiographic image capturing apparatus 1 reads the image data D as the main image at the same time as the detection operation of the irradiation start of the radiation when the reading process of the image data D is completed. The transmission processing for transmitting the preview image data based on the image data D to the console 58 is started.

  In the present embodiment, the control unit 22 of the radiographic image capturing apparatus 1 transmits, as preview image data, thinned data Dt obtained by thinning and extracting data from the read image data D at a predetermined rate to the console. It has become.

  FIG. 22 shows a case where the transmission process of the preview image data is completed while the charge accumulation state continues after the above-described single detection operation. As described above, For example, the time required for transmission processing may become longer depending on the degree of congestion of the communication line. In this embodiment, in such a case, the transmission process of the preview image data cannot be completed within the duration of the charge accumulation state after the above-described one detection operation. As shown in FIG. 6, the offset data O reading process may be started during the transmission process.

  However, in this embodiment, in such a case, the transmission process of the preview image data is stopped and the reading process of the offset data O is started as in the conventional case. The reason for this configuration in the present embodiment will be described in the following description.

  Hereinafter, how to extract the thinned data Dt and how to display the preview image p_pre on the console 58 will be described with some examples.

[Extraction method 1]
For example, as shown in FIG. 27, image data D read from the radiation detection element 7 (n, m) in the n-th row and the m-th column of the detection unit P (see FIG. 4 and FIG. 7) of the radiographic imaging device 1. Is represented by D (n, m), the control means 22 of the radiographic image capturing apparatus 1 preliminarily stores the read image data D (n, m), for example, as shown by hatching in the figure. An image read from each radiation detection element 7 connected to the scanning line 5 designated at a ratio of one for each of the lines L1 to Lx of the predetermined number (four in the case of FIG. 27) of the scanning lines 5. It is possible to extract the data D (n, m) and extract it as the thinned data Dt.

[Extraction method 1-1]
At that time, the control means 22 of the radiographic image capturing apparatus 1 sets the other end of the detection unit P from the scan line 5 existing on one end side of the detection unit P among the designated scanning lines 5 as shown in FIG. The scanning line 5 for extracting the image data D is directed toward the scanning line 5 existing on the side (that is, in the example of FIG. 27, the scanning line 5 on the lower end side not shown from the scanning line 5 on the upper end side in the figure). While shifting, the image data D read from each radiation detection element 7 connected to each designated scanning line 5 is sequentially extracted. Then, it is possible to configure such that it is sequentially transmitted to the console 58 as the thinned data Dt.

  On the console 58 side, when the thinned data Dt extracted as described above is transmitted as data for the preview image from the radiation image capturing apparatus 1, every time the data for the preview image is transmitted, A preview image p_pre is generated. Then, the console 58 has a position on the display unit 58a (see FIGS. 11 and 12) corresponding to the position on the detection unit P of the radiation image capturing apparatus 1 of the radiation detection element 7 from which the preview image data is read. In addition, the generated preview image p_pre is displayed, and the preview image p_pre is sequentially wiped on the display unit 58a.

  At this time, at the time when the data for the preview image is transmitted from the radiographic image capturing apparatus 1, the offset data O (to be described later) obtained by the current capturing is not yet transmitted.

Therefore, for example, as offset data corresponding to preview image data (that is, thinning data Dt in the present embodiment), temporary offset data O ^* is assigned in advance to each radiation detection element 7 of the radiation image capturing apparatus 1. The console 58 subtracts the provisional offset data O ^* from the transmitted preview image data, and the preview image is based on the subtracted value (corresponding to the true image data D ^* described above). It can be configured to generate p_pre.

  Further, as the offset data to be subtracted from the preview image data, the offset data O transmitted from the radiation image capturing apparatus 1 at the previous capturing time performed using the radiation image capturing apparatus 1 is stored, and this previous time is stored. The offset data O at the time of shooting can be used as offset data to be subtracted from the preview image data transmitted at the time of shooting this time.

  Although detailed explanation is omitted, when the compressed data is transmitted when the thinned data Dt, the image data D, and the like are transmitted from the radiation image capturing apparatus 1, the console 58 stores the compressed data. Needless to say, a process of decompressing and restoring the original data is performed.

  On the other hand, as shown in FIG. 28 and FIG. 29, the console 58 has an “OK” button 60a, that is, a button for instructing to approve the preview image p_pre in the vicinity of the preview image p_pre displayed on the display unit 58a, and “ "NG" button 60b, that is, a button for instructing that the preview image p_pre is rejected (that is, not approved) is displayed.

  If the radiologist who has seen the preview image p_pre displayed as a wipe determines that the subject is not properly captured in the image and needs to be re-imaged, the user clicks the “NG” button 60b. . When it is determined that re-imaging is necessary and the “NG” button 60 b is clicked, the console 58 transmits a stop signal to the radiographic image capturing apparatus 1.

  When the stop signal is transmitted from the console 58, the control means 22 of the radiographic image capturing apparatus 1 performs the subsequent processes shown in FIG. 22, that is, the continuation state of the charge accumulation state when the charge accumulation state is continued. In addition, when the offset data O reading process and the subsequent processes are started, each process such as the offset data O reading process is stopped. This is because a normal radiographic image p cannot be obtained even if the radiographic image p is generated based on the image data D or the like.

  In this case, in order to prepare for re-imaging, the control means 22 of the radiographic image capturing apparatus 1 resets the first radiation detection elements 7 shown in FIG. 22 and reads leak data dleak before radiographic image capturing. It returns to the state which performs detection processing of these.

  When the radiographer who has viewed the preview image p_pre clicks the “OK” button 60b, a stop signal is not transmitted from the console 58 to the radiographic image capturing apparatus 1, and the control means of the radiographic image capturing apparatus 1 is used. 22 continues each subsequent process.

  With this configuration, for example, as shown in FIG. 22, the detection operation is performed once after the read processing of the image data D as the main image, and the state for the preview image is changed to the charge accumulation state and continued. When the data transmission process is completed, all the data for the preview image (thinned data Dt in the present embodiment) is transmitted from the radiation image capturing apparatus 1 to the console 58.

  Therefore, in this case, as shown in FIG. 29, the preview image p_pre is all displayed on the display unit 58a of the console 58 (that is, the preview image p_pre based on all the thinned data Dt is displayed). . Therefore, the radiologist looks at the preview image p_pre displayed on the display unit 58a to check whether or not the subject is properly captured in the image, and confirms whether re-imaging is necessary. It becomes possible to judge.

  On the other hand, as shown in FIG. 26, even when the transmission process of the preview image data is not completed during one detection operation and the charge accumulation state, the radiologist can accurately perform the above determination. To the extent, the preview image data can be transmitted to the console 58.

  That is, the amount of data for the preview image that can be transmitted within a short period in which one detection operation is performed after the reading process of the image data D as the main image is small, and the preview image displayed on the console 58 within this period Even in the case where p_pre can be displayed only to the extent shown in FIG. 28, for example, in the present embodiment, as described above, transmission of the data for the preview image is also performed while the subsequent charge accumulation state continues. Continued.

  Therefore, after the duration of the charge accumulation state (that is, at the start of the offset data O reading process), even if all the preview images p_pre cannot be displayed as shown in FIG. 29, a considerable amount of preview images are displayed. For example, as shown in FIG. 30, the radiographer makes a sufficient judgment as to whether the subject is properly captured in the image and whether re-imaging is necessary. The preview image p_pre can be displayed to the extent that it can be performed.

  Therefore, if configured as described above, the preview image p_pre can be displayed on the console 58 with sufficient accuracy so that at least the radiographer can accurately determine the necessity of re-imaging.

[Extraction method 1-2]
On the other hand, when extracting the thinned data Dt as shown in the extraction method 1 (see FIG. 27), the image data D of the designated scanning lines 5 is extracted as in the extraction method 1-1. Instead of extracting the thinned data Dt while shifting the scanning line 5 to be extracted from one end side to the other end side of the detection unit P, for example, as shown in FIG. 31, it exists in the central portion Ce of the detection unit P. The image data D is sequentially extracted while shifting the scanning line 5 for extracting the image data D from the scanning line 5 toward the scanning line 5 existing at the end E of the detection unit P, and the thinned data Dt is sent to the console 58. It is also possible to configure to transmit sequentially.

  In this case, although illustration is omitted, on the console 58 side, the preview image p_pre is wiped and displayed so as to expand from the center to the end of the display area of the preview image p_pre on the display unit 58a. Become.

  With this configuration, for example, when the radiographic imaging device 1 is used for imaging radiographic images for diagnosis in medicine (also referred to as medical images), a lesioned part of a patient is usually captured as a radiographic image. As shown above, the preview image p_pre is displayed first from the center, so that if the patient's lesion is accurately captured, the lesion is compared. It is displayed on the preview image p_pre at an early stage.

  Therefore, as shown in FIG. 26, whether or not the radiographer has been photographed even when the data for all the preview images cannot be transmitted from the radiation image photographing apparatus 1 while the charge accumulation state continues. The imaged portion of the lesion that is the target to be confirmed is accurately displayed on the preview image p_pre.

  Therefore, by configuring as described above, it is possible to display the preview image p_pre to such an extent that the radiologist can accurately determine whether or not at least an imaging target site such as a lesion is appropriately captured in the image. It becomes. Therefore, if configured as described above, the preview image p_pre can be displayed on the console 58 with sufficient accuracy so that at least the radiographer can accurately determine the necessity of re-imaging.

[Extraction method 1-3]
By the way, in the case of the above-described extraction method 1-1 and extraction method 1-2, for example, as shown in FIG. 26, when data for all preview images cannot be transmitted from the radiation image capturing apparatus 1 while the charge accumulation state continues. For example, as shown in FIG. 30, a part of the preview image p_pre displayed on the display unit 58a of the console 58 is not displayed. However, there are cases where it is desired to avoid the occurrence of such a non-displayed portion.

  Therefore, in such a case, first, the preview image p_pre is displayed on the display unit 58a of the console 58 at a low resolution without any non-displayed portion, and the displayed preview image p_pre is displayed from the low resolution state. It is possible to sequentially transmit the preview image data from the radiation image capturing apparatus 1 to the console 58 in the order of transition to the high resolution state.

  Specifically, for example, as shown in FIG. 27, when the image data D of each scanning line 5 designated at a ratio of 1 to 4 is transmitted as the thinned data Dt, first, for example, the enlargement of FIG. As indicated by the solid line in the image diagram, the image data D of the lines L1, L17, L33,... Of the scanning line 5 is extracted at a rate of 1 out of 16 and transmitted to the console 58.

  Subsequently, among the remaining thinned data Dt, as shown by a one-dot chain line in FIG. 32, lines L9, L25, L41 of the scanning line 5 in the middle of the lines L1, L17, L33,. .. Are extracted and transmitted to the console 58. Finally, as shown by the broken lines in FIG. 32, each of the lines L1, L9, L17, L25, L33,. The image data D of the lines L5, L13, L21,... Of the scanning line 5 is extracted and transmitted to the console 58.

  At this time, the thinned data Dt is shifted while the scanning line 5 is shifted from one end side to the other end side of the detection portion P as in the extraction method 1-1 (see FIG. 28, FIG. 29, etc.). It may be configured to extract, or, as in the extraction method 1-2 (see FIG. 31), the scanning existing at the end E of the detecting unit P from the scanning line 5 existing at the central portion Ce of the detecting unit P. It is possible to extract the thinned data Dt while shifting the scanning line 5 toward the line 5.

  Then, the console 58 extracts the thinned data Dt extracted from the radiographic imaging apparatus 1 at a ratio of one to the first 16 scanning lines 5, that is, the lines L1, L17, L33,. At the stage where each image data D (refer to the solid line) is transmitted, the preview image p_pre is wiped and displayed at a low resolution on the display unit 58a, for example, as shown in FIG.

  Subsequently, the console 58 is in a stage where the image data D of the lines L9, L25, L41,... (Refer to the one-dot chain line in FIG. 32) of the scanning line 5 is transmitted as the thinned data Dt from the radiation image capturing apparatus 1. As shown in FIG. 33B, the image data D of the lines L1, L17, L33,... Already received on the scanning line 5 and the lines L9, L25,. Based on the image data D of L41,..., The preview image p_pre is displayed at a medium resolution on the display unit 58a so that the vertical resolution of the preview image p_pre shown in FIG. Wipe display.

  Finally, at the stage where each image data D of the lines L5, L13, L21,... (See the broken line in FIG. 32) of the remaining scanning lines 5 is transmitted as the thinned data Dt from the radiation image capturing apparatus 1. 33 (C), the image data D of the lines L1, L9, L17, L25,... Of the already received scanning line 5 and the lines L5, L13 of the intermediate scanning line 5 transmitted thereto. , L21,... On the display unit 58a so that the vertical resolution of the intermediate resolution preview image p_pre shown in FIG. The preview image p_pre is wiped and displayed at the resolution.

  In this way, by configuring the thinned data Dt (that is, the data for the preview image) to be sequentially transmitted to the console 58 in the order as described above, the preview image p_pre is displayed on the display unit 58a of the console 58 at a low level. It is possible to perform wipe display in a state where the resolution state transitions to the high resolution state.

  In the case shown in FIG. 22, data for all preview images is transmitted from the radiographic imaging apparatus 1 to the console 58 during the continuation of the charge accumulation state, so that the preview is displayed on the display unit 58a of the console 58. The image p_pre is displayed in the high resolution state shown in FIG.

  Further, as shown in FIG. 26, even when the data for all the preview images cannot be transmitted from the radiographic image capturing apparatus 1 while the charge accumulation state is continued, the above one detection operation is terminated. Further, until the continuation of the charge accumulation state is completed, a sufficient amount of data for the preview image can be transmitted from the radiation image capturing apparatus 1 to the console 58.

  Therefore, the preview image p_pre can be displayed on the display unit 58a of the console 58 at least at the medium resolution state shown in FIG. 33B, and the radiologist can make the above confirmation and judgment sufficiently accurate. It is possible to display the preview image p_pre to the extent that it can be performed. Therefore, if configured as described above, the preview image p_pre can be displayed on the console 58 with sufficient accuracy so that at least the radiographer can accurately determine the necessity of re-imaging.

  In the extraction method 1-3, the image data D is extracted as the thinned data Dt for each scanning line 5 designated as shown in FIG. For this reason, as shown in FIGS. 33A to 33C, the preview image p_pre displayed on the display unit 58a of the console 58 is gradually increased in resolution in the vertical direction in the figure as described above. However, image data D is displayed for each pixel (that is, for each radiation detection element 7) in the horizontal direction in the figure. Therefore, the resolution in the horizontal direction in the figure of the preview image p_pre remains one pixel and does not change.

[Extraction method 2]
On the other hand, the method of extracting the thinned-out data Dt as the preview image data is not limited to the above case, and although not shown, for example, a total of 16 radiation detections of 4 × 4 pixels, that is, 4 rows and 4 columns are detected. The image data D is extracted from the image data D by extracting the image data D from the 16 pieces of image data D (n, m) read from the element 7 (n, m) at a rate of one. It is also possible to extract the thinned data Dt created by thinning out at a predetermined rate.

[Extraction method 2-1]
Also in this case, for example, as in the case of the extraction method 1-1 described above (see FIGS. 28 to 30), the control means 22 of the radiographic image capturing apparatus 1 uses each thinning data Dt as one end of the detection unit P. It is possible to configure such that data is sequentially extracted from the side toward the other end side and is sequentially transmitted to the console 58. Then, the preview image p_pre is wiped and displayed on the display unit 58a of the console 58 in the same manner as in the case shown in FIGS.

  In this case and in the case of the extraction method 2-2 described below, the thinning data Dt is further thinned to, for example, 1/4 in the horizontal direction in the figure from the case of FIG. Compared to the cases of 1 and 1-2, the resolution in the horizontal direction in the figure of the preview image p_pre is about ¼ that in the case shown in FIGS.

  With this configuration, as shown in FIG. 26, even if the transmission process of the preview image data is not completed during one detection operation and the charge accumulation state, as shown in FIG. The data for the preview image is transmitted to the console 58 to such an extent that the radiographer can sufficiently determine whether the subject is properly captured in the image or whether re-imaging is necessary. It becomes possible.

[Extraction method 2-2]
Further, as in the case of the above extraction method 1-2 (see FIG. 31), each thinned data Dt is sequentially extracted from the central portion Ce to the end portion E of the detection unit P and sequentially transmitted to the console 58. It is also possible to configure so as to. Then, the preview image p_pre is wiped and displayed on the display unit 58a of the console 58 in the same manner as in the case of the extraction method 1-2 described above.

  With this configuration, as in the case of the extraction method 1-2 described above, as shown in FIG. 26, data for all preview images is transmitted from the radiation image capturing apparatus 1 while the charge accumulation state continues. Even if this is not possible, the imaging part of the lesion that is the target for which it is desired to check whether or not the radiographer has been imaged will be accurately displayed on the preview image p_pre.

  Therefore, it is possible to display the preview image p_pre to such an extent that the radiologist can accurately determine whether or not at least an imaging target site such as a lesion is appropriately captured in the image. Therefore, if configured as described above, the preview image p_pre can be displayed on the console 58 with sufficient accuracy so that at least the radiographer can accurately determine the necessity of re-imaging.

[Extraction method 3-3]
As in the case of the extraction method 1-3 described above, the preview image p_pre is displayed on the display unit 58a of the console 58 at a low resolution, and the displayed preview image p_pre is changed from the low resolution state to the high resolution state. The thinning data Dt may be sequentially transmitted from the radiographic imaging apparatus 1 to the console 58 in an order that makes a transition to the state.

  In this case, for example, first, the thinning data Dt extracted from the image data D (n, m) of, for example, 16 × 16 pixels by the radiation image capturing apparatus 1 at a ratio of one is transmitted to the console 58, and FIG. As shown in the enlarged image diagram of (A), a low-resolution preview image p_pre is displayed on the display unit 58a of the console 58 as a wipe.

  Subsequently, the radiographic imaging device 1 transmits, to the console 58, thinning data Dt extracted at a rate of one out of, for example, 8 × 8 pixel image data D (n, m) among the remaining thinning data Dt. Then, as shown in the enlarged image diagram of FIG. 34 (B), a preview image p_pre having a medium resolution is displayed on the display portion 58a of the console 58 as a wipe.

  Finally, in the radiographic image capturing apparatus 1, the remaining thinned data Dt, that is, the remaining thinned data Dt extracted at a rate of one out of 4 × 4 pixel image data D (n, m) is displayed on the console 58. As shown in the enlarged image diagram of FIG. 34C, the high-resolution preview image p_pre is displayed on the display unit 58a of the console 58 as a wipe.

  With this configuration, as shown in FIG. 26, even if the data for all the preview images cannot be transmitted from the radiographic image capturing apparatus 1 while the charge accumulation state continues, the above-described one-time operation is performed. Between the end of the detection operation and the end of the continuation of the charge accumulation state, a sufficient amount of preview image data can be transmitted from the radiographic imaging apparatus 1 to the console 58.

  Therefore, the preview image p_pre can be displayed on the display unit 58a of the console 58 at least at the medium resolution state shown in FIG. 34B, and the radiologist can make the above confirmation and judgment sufficiently accurate. It is possible to display the preview image p_pre to the extent that it can be performed. Therefore, if configured as described above, the preview image p_pre can be displayed on the console 58 with sufficient accuracy so that at least the radiographer can accurately determine the necessity of re-imaging.

  In the extraction method 2-3, as shown in FIGS. 34A to 34C, the preview image p_pre displayed on the display unit 58a of the console 58 is not limited to the vertical resolution in the figure. Wipe display is performed so that the resolution in the middle and horizontal directions is gradually increased.

[Reading process of offset data O]
As described above, the control means 22 of the radiographic image capturing apparatus 1 reads the offset data O as shown in FIGS. 22, 25, and 26 when a predetermined time has elapsed since the transition to the charge accumulation state. It is supposed to be processed.

  When the radiologist who viewed the preview image p_pre determines that re-imaging is necessary and clicks the “NG” button 60b, the console 58 transmits a stop signal to the radiographic image capturing apparatus 1, and the radiographic image is displayed. The control unit 22 of the photographing apparatus 1 stops the continuation state of the charge accumulation state performed at that time, or stops the offset data O reading process and subsequent processes, and is shown in FIGS. As described above, the process returns to the state in which the detection process such as the reset process of each radiation detection element 7 for the first time and the reading process of the leak data dleak before radiographic image capturing is performed.

  In the reading process of the offset data O, in the present embodiment, the control unit 22 in the reading process of the image data D as the main image from the gate driver 15b to the detection line from the reading start line of the scanning line 5, that is, in the case of FIG. The gate driver 15b sequentially applies the on-voltage to each line L of the scanning line 5 with the same period τ when the on-voltage is sequentially applied to the lines L5 to Lx and L1 to L4 of the scanning line 5. The offset data O is read out.

  That is, the control unit 22 of the radiographic imaging device 1 performs a series of processing sequences (from detection processing to charge processing) until the reading processing of the image data D in a state in which no radiation is irradiated after the reading processing of the image data D as the main image. The same processing sequence as the processing sequence from the storage state to the reading processing) is repeated, and the reading processing of the offset data O is performed.

  With this configuration, the on-voltage applied to the scanning line 5 before switching to the charge accumulation state is switched to the off-voltage, and then the on-voltage applied to the scanning line 5 in the readout process after the charge accumulation state is turned off. The time Tac (see FIGS. 16, 20 and 25; hereinafter referred to as the effective accumulation time Tac) until switching to the processing sequence until the reading processing of the image data D as the main image and the reading processing of the offset data O It is the same time with the processing sequence up to.

  As described above, dark charges are constantly generated in each radiation detection element 7, and each radiation detection element is in the charge accumulation state while each TFT 8 is in the off state, that is, during the above-described effective accumulation time Tac. Dark charges are accumulated in 7. The amount of dark charge accumulated in the radiation detection element 7 varies depending on the length of the effective accumulation time Tac. However, if the length of the effective accumulation time Tac is the same, the amount of dark charge accumulated is the same. Become.

On the other hand, the image data D read out from each radiation detection element 7 as a main image is a so-called true image caused by only the charges generated in the radiation detection element 7 due to radiation irradiation, as shown in the following equation (1). The data D ^* , the offset due to the amount of residual charge existing in the radiation detection element 7 at the moment when the TFT 8 is switched from the on state to the off state before the charge accumulation state as described above, and the effective accumulation time thereafter This is the sum of the offset due to the amount of dark charge generated in the radiation detection element 7 within Tac.
D = D ^* + offset due to residual charge + offset due to dark charge (1)

Also, the offset data O read from each radiation detection element 7 in the offset data O read process is the offset due to the amount of residual charge existing in the radiation detection element 7, as shown in the following equation (2). This is the sum of the offset due to the amount of dark charge generated in the radiation detection element 7 within the effective accumulation time Tac.
O = offset due to residual charge + offset due to dark charge (2)

  In the present embodiment, after the read process of the image data D as the main image, the read process of the leak data dleak and the like are performed before the read process of the offset data O, so that the residual charge existing in each radiation detection element 7 is obtained. As described above, the amount of the image data D is the same during the reading process of the image data D and the reading process of the offset data O.

  As described above, if the same processing sequence as the series of processing up to the reading process of the image data D as the main image is repeated to perform the reading process of the offset data O, the image data D The effective accumulation time Tac is the same between the reading process and the offset data O reading process, and the amount of dark charge accumulated in each radiation detection element 7 is also the same.

  As described above, in the present embodiment, with the configuration described above, the offset due to the residual charge superimposed on the image data D as the main image and the offset due to the residual charge in the offset data O are configured. Become the same value, and the offset due to the dark charge superimposed on the image data D as the main image and the offset due to the dark charge in the offset data O also have the same value.

Therefore, in the present embodiment, the offset data O is simply subtracted from the image data D for each radiation detection element 7 without performing any arithmetic processing on the image data D and the offset data O as the main image ( That is, only by subtracting the offset data O expressed by the above equation (2) from the image data D expressed by the above equation (1)), it is caused only by the charges generated in the radiation detecting element 7 due to the irradiation of radiation. It is possible to reliably obtain the true image data D ^* .

In other words, in other words, in the radiographic image capturing apparatus 1 according to the present embodiment, the true image data D ^* is reliably obtained by simply subtracting the offset data O from the image data D obtained as the main image. In order to be obtained, the processing configuration as described above is adopted.

  Further, as described above, this can be realized by repeating the same processing sequence as the series of processing sequence up to the reading processing of the image data D as the main image to perform the reading processing of the offset data O. Therefore, there is an advantage that the control configuration of each process in the control means 22 of the radiographic image capturing apparatus 1 can be constructed very easily.

[Transmission of remaining image data D, etc.]
Then, when the preview image data transmission process is completed while the charge accumulation state continues as shown in FIG. 22, the control unit 22 of the radiographic image capturing apparatus 1 ends the offset data O read process. Thereafter, offset data O corresponding to the thinned data Dt that has already been transmitted (that is, 1/4 offset data O corresponding to 1/4 image data D (see FIG. 27) transmitted as the thinned data Dt) is transmitted. The remaining 3/4 image data D other than the data Dt is transmitted, and finally the remaining 3/4 offset data O other than the offset data O corresponding to the thinned data Dt is transmitted to the console 58, respectively. Yes.

  As shown in FIG. 26, when the data transmission process for the preview image is not completed while the charge accumulation state is continued, the control unit 22 of the radiographic image capturing apparatus 1 reads the offset data O. After the process is completed, the data for the untransmitted preview image that could not be transmitted is transmitted to the console 58 prior to the transmission of each data described above.

[Generation of radiation images]
In addition, when the console 58 receives untransmitted preview image data, that is, untransmitted thinned data Dt or offset data O corresponding to the thinned data Dt, from the radiographic imaging device 1, the thinned data Dt, that is, the figure. 27, the true image data D ^* is calculated by subtracting the corresponding offset data O from the quarter image data D.

When the remaining 3/4 of the image data D and the remaining 3/4 of the offset data O are transmitted from the radiographic image capturing apparatus 1, they are subtracted, and the remaining 3/4 of the data is subtracted. The true image data D ^* described above is calculated for the image data D.

The console 58 performs precise image processing such as gain correction, offset correction, defective pixel correction, and gradation processing according to the imaging region based on the calculated true image data D ^* to obtain the final radiation image p. Is supposed to generate. In the present embodiment, when the radiation image p is generated, the console 58 displays the generated radiation image p instead of the preview image p_pre (see FIG. 29) displayed on the display unit 58a. .

  Further, when a series of radiographic image capturing is completed, the console 58 receives information on each radiographic image p and the like, for example, a medical image management system (Picture Archiving and Communication System: not shown) by the operation of the radiographer. Necessary processing such as transmission to PACS) is performed.

  As described above, according to the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to the present embodiment, first, the control unit 22 of the radiographic image capturing apparatus 1 uses the leak data dleak and irradiation read before radiographic image capturing. Based on the start detection data d, the start of radiation irradiation can be accurately detected.

  Therefore, even when an interface cannot be constructed (or no interface is constructed) between the radiation imaging apparatus and the radiation generation apparatus 55 (see FIGS. 11 and 12), radiation irradiation is performed by the radiation imaging apparatus 1 itself. The start can be accurately detected, and radiographic imaging can be appropriately performed.

  The control unit 22 of the radiographic image capturing apparatus 1 is not only during one detection operation after the reading process of the image data D as the main image, but also during a period including a period during which the charge accumulation state continues thereafter. Then, the preview image data is transmitted to the console 58. Then, the console 58 displays the preview image p_pre on the display unit 58a based on the data for the preview image transmitted from the radiation image capturing apparatus 1.

  Therefore, as shown in FIG. 22, even if the data for the preview image cannot be transmitted during one detection operation after the reading process of the image data D, all the preview images are displayed during the subsequent charge accumulation state. If the data for use can be transmitted to the console 58, for example, as shown in FIG. 29, the entire preview image p_pre can be accurately displayed on the display unit 58a of the console 58.

  In addition, as shown in FIG. 26, even if the data for all the preview images cannot be transmitted to the console 58 during one detection operation after the reading process of the image data D or during the subsequent continued charge accumulation state. It is possible to transmit a considerable amount of preview image data from the radiographic image capturing apparatus 1 to the console 58 during the time when one detection operation is performed and the duration of the charge accumulation state.

  Therefore, even if the preview image p_pre cannot all be displayed on the display unit 58a of the console 58, for example, as shown in FIG. 30, the radiologist needs to re-photograph whether the subject is properly captured in the image. The preview image p_pre can be displayed to such an extent that it can be determined with sufficient accuracy.

  Therefore, according to the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to the present embodiment, the preview image p_pre is sufficiently accurately displayed on the console 58 so that at least the radiographer can accurately determine whether or not re-imaging is necessary. It can be displayed.

  Further, in the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to the present embodiment, as illustrated in FIGS. 22 and 26, regardless of whether the transmission process of the preview image data is completed or not, After the reading process of the image data D as the main image, when the detection operation and the continuation of the charge accumulation state are completed, the reading process of the offset data O is started immediately.

  Therefore, for example, as in the case of the conventional apparatus or system shown in FIG. 24, after the reading process of the image data D as the main image, the reset of each radiation detection element 7 is completed until the transmission process of the data for the preview image is completed. Compared to the case where the process is repeated and then the state is shifted to the charge accumulation state, the offset data O reading process can be started earlier and each data can be transmitted to the console 58.

  Therefore, it is possible to perform one radiographic image capturing in a short time, and the radiographer can perform image capturing one after another using the radiographic image capturing apparatus 1. Therefore, the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 are easy to use for the radiographer.

  In the above embodiment, the control unit 22 of the radiographic image capturing apparatus 1 reads the preview image data based on the read image data D (in the above embodiment, thinning out) after the read processing of the image data D as the main image. When starting the transmission process of transmitting the data Dt) to the console 58 and simultaneously performing the readout process of the leak data dleak and the reset process of each radiation detection element 7 (that is, when performing the detection operation), The case where the reset processing of the radiation detection element 7 is performed by sequentially applying the ON voltage to the scanning lines 5 of the detection unit P from the gate driver 15b of the scanning driving unit 15 one by one has been described.

  However, instead of configuring in this way, the on-voltage is sequentially applied to each scanning line 5 of the detection unit P a predetermined number of times, so that the leak data dleak is read out and each radiation detection element 5 is processed. It is also possible to configure so that the reset process is alternately performed. That is, it is also possible to configure so that the above-described one process is performed for a plurality of predetermined times.

  For example, in FIG. 25 described above, after the reading process of the image data D as the main image, the reading process of the leak data dleak (see “L” in the figure) and the resetting process of each radiation detection element 7 (“R” in the figure). 1) is performed once, that is, when a single process is performed. However, when configured as described above, this single process is repeated a plurality of times after the read processing of the image data D. .

  The same applies when the above-described detection method 2 is employed, and a transmission process for transmitting preview image data based on the read image data D to the console 58 is started after the read process of the image data D as the main image. At the same time, when the reading process of the irradiation start detection data d is performed, the reading process of the irradiation start detection data d is sequentially performed from the gate driver 15b of the scanning drive unit 15 to each scanning line 5 of the detection unit P. Instead of applying one time at a time (that is, instead of performing one process only once), each scanning line 5 is configured to be sequentially applied with a predetermined number of times. It is also possible.

  At that time, after the reading process of the image data D as the main image, how many times the above-described one process is performed is determined based on a time allowed as a time required for one radiographic image capturing. Can be determined as appropriate.

  In the above-described embodiment, as shown in FIG. 26, for example, the case where the transmission process of the preview image data is performed until immediately before the offset data O reading process has been described. The preview image data transmission process is performed from the state to the moment when the process shifts to the offset data O reading process.

  Even if configured in this way, there is no problem as long as the reading process of the offset data O is started after the transmission process of the data for the preview image has been completed without fail, but some time is allowed. Therefore, for example, it is possible to configure so that the transmission process of the preview image data is terminated before the process of reading the offset data O from the charge accumulation state.

  Further, it goes without saying that the present invention is not limited to the above-described embodiments and modifications, and can be appropriately changed without departing from the gist of the present invention.

DESCRIPTION OF SYMBOLS 1 Radiographic imaging device 5 Scanning line 6 Signal line 7 Radiation detection element 8 TFT (switch means)
15 Scanning drive means 17 Reading circuit 22 Control means 39 Connector (communication means)
41 Antenna device (communication means)
50 Radiation imaging system 58 Console 58a Display unit Ce Center part of detection unit D Image data d Irradiation start detection data dleak Leak data Dt Thinning-out data (data for offset image)
E End of detection unit O Offset data P Detection unit p_pre Preview image q Charge r Small region τ Period

Claims (12)

A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other, and a plurality of radiation detection elements arranged in a two-dimensional manner in each small region partitioned by the plurality of scanning lines and the plurality of signal lines A detector comprising:
Scan driving means for applying an on voltage or an off voltage to each of the scanning lines;
Switch means connected to each of the scanning lines and causing the signal lines to discharge charges accumulated in the radiation detection element when an on-voltage is applied;
A readout circuit that converts the electric charge emitted from the radiation detection element into image data and reads the image data;
The charge leaked from each radiation detection element via each switch means in a state where an off voltage is applied to each scan line from the scan driving means to turn off each switch means before radiographic image capturing. The leak data reading process for converting the data into leak data and the reset process of the radiation detection elements performed by sequentially applying an on-voltage to the scan lines from the scan driving unit are alternately performed, and the read Control means for detecting the start of radiation irradiation based on the leak data;
With
The control means includes
When the start of radiation irradiation is detected, an off voltage is applied to each scanning line from the scanning driving unit, and after passing through a charge accumulation state in which each switching unit is turned off, at least the scanning driving unit and the readout circuit are After performing control and reading processing of image data from the radiation detection element,
At the same time as starting the transmission process for transmitting preview image data based on the read image data to the console, the reset process of each radiation detection element, which is alternately performed with the read process of the leak data, is detected from the scan driving means. The on-voltage is sequentially applied to each of the scanning lines of the unit, and the leakage data reading process and the resetting process of the radiation detection elements are alternately performed.
Thereafter, in a state where no radiation is applied, an off voltage is applied to each scanning line from the scanning drive means for the same time as the charge accumulation state before the image data read processing, thereby turning off the switch means. Continue the charge accumulation state,
A radiographic image characterized in that, if the transmission processing of the preview image data is not completed when the continuation of the charge accumulation state is completed, the transmission processing is stopped and then the offset data reading processing is performed. Shooting device.   The control means, after causing the image data to be read out, starts transmission processing for transmitting preview image data based on the read-out image data to a console, and at the same time reads out the leak data and the respective radiations When the reset process of the detection element is alternately performed, the reset process of each of the radiation detection elements alternately performed with the reading process of the leak data is performed on-voltage from the scan driving unit to each of the scanning lines of the detection unit. In this case, the on-voltage is sequentially applied to each of the scanning lines a predetermined number of times, so that the leakage data reading process and the radiation detecting elements are The radiographic imaging apparatus according to claim 1, wherein the reset processing is alternately performed.   The control means does not perform the leak data read processing after the image data read processing and before the offset data read processing, and performs only the reset processing of each radiation detection element before radiographic imaging. The on-voltage is sequentially applied from the scanning driving means to the scanning lines of the detection unit at the same cycle as the reset processing of the radiation detecting elements alternately performed with the leakage data reading processing. The radiographic imaging device according to claim 1 or 2. A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other, and a plurality of radiation detection elements arranged in a two-dimensional manner in each small region partitioned by the plurality of scanning lines and the plurality of signal lines A detector comprising:
Scan driving means for applying an on voltage or an off voltage to each of the scanning lines;
Switch means connected to each of the scanning lines and causing the signal lines to discharge charges accumulated in the radiation detection element when an on-voltage is applied;
A readout circuit that converts the electric charge emitted from the radiation detection element into image data and reads the image data;
Prior to radiographic image capture, the scanning drive means sequentially applies an on-voltage to each scanning line to cause the irradiation start detection data to be read, and radiation irradiation is performed based on the read irradiation start detection data. Control means for detecting that it has started;
With
The control means includes
When the start of radiation irradiation is detected, an off voltage is applied to each scanning line from the scanning driving unit, and after passing through a charge accumulation state in which each switching unit is turned off, at least the scanning driving unit and the readout circuit are After performing control and reading processing of image data from the radiation detection element,
At the same time as the transmission processing for transmitting the preview image data based on the read image data to the console is started, the irradiation start detection data read processing is turned on for each scanning line of the detection unit from the scanning driving means. Apply voltage one by one in sequence,
Thereafter, in a state where no radiation is applied, an off voltage is applied to each scanning line from the scanning drive means for the same time as the charge accumulation state before the image data read processing, thereby turning off the switch means. Continue the charge accumulation state,
A radiographic image characterized in that, if the transmission processing of the preview image data is not completed when the continuation of the charge accumulation state is completed, the transmission processing is stopped and then the offset data reading processing is performed. Shooting device.   The control means starts the transmission process for transmitting the preview image data based on the read image data to the console after performing the image data read process, and simultaneously performs the irradiation start detection data read process. When performing the irradiation start detection data reading process, the on-voltage is sequentially applied to the respective scanning lines of the detection unit from the scanning drive unit, instead of being applied to the respective scanning lines. The radiographic imaging apparatus according to claim 4, wherein each of the on-voltages is sequentially applied a predetermined number of times.   The control means performs a reset process of each radiation detection element after the image data read process, instead of performing a read process of the irradiation start detection data. 6. The radiographic imaging apparatus according to claim 4, wherein an on-voltage is sequentially applied from the scanning driving unit to the scanning lines of the detection unit at the same cycle as the readout process.   7. The control unit according to claim 1, wherein after the offset data reading process, the control unit transmits untransmitted image data and the offset data of the image data to the console. The radiographic imaging device according to item.   The control means transmits to the console thinned data extracted by thinning out the data from the read image data at a predetermined rate as the data for the preview image. The radiographic imaging apparatus as described in any one of these.   The control means reads out from each radiation detection element connected to each scanning line designated at a ratio of one for every predetermined number of scanning lines among the scanning lines of the detection unit. The radiographic image capturing apparatus according to claim 8, wherein the image data is extracted and used as the thinning data.   The control means extracts the image data from the scanning line existing at the center of the detection unit to the scanning line existing at the end of the detection unit among the designated scanning lines. The image data read from each radiation detection element connected to each designated scanning line is sequentially extracted while the scanning lines are shifted, and sequentially transmitted to the console as the thinned data. The radiographic imaging apparatus according to claim 9.   The control means sets the image data extracted as the thinned data in an order in which the preview image displayed on the console transitions from a low resolution state to a high resolution state based on the thinned data. The radiographic image capturing apparatus according to claim 8, wherein the radiographic image capturing apparatus transmits the image to the console. The radiographic image capturing apparatus according to any one of claims 1 to 11, further comprising a communication unit;
A console that generates a preview image based on the data for the preview image transmitted from the radiation image capturing apparatus and displays the preview image on the display unit;
With
The console generates the preview image based on the preview image data each time the preview image data is transmitted from the radiographic imaging device, and reads the preview image data. The generated preview image is displayed at a position on the display unit corresponding to a position on the detection unit of the radiographic image capturing device of the radiation detection element thus formed, and the preview image is displayed on the display unit. A radiographic imaging system characterized by having a wipe display on top.

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