JP2012152477A - Radiation imaging system and radiation imaging apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiation imaging system capable of imaging in a short cycle time even in the case of continuous imaging.SOLUTION: The radiation imaging system 50 includes a control means 22 of a radiation imaging apparatus 1 for creating thinned data Dt by thinning image data D at a prescribed percentage from the image data D read from respective radiation detection elements 7 every time respective radiation imaging is completed to transmit to a console 58, in a series of radiation imaging, wherein the console 58 repeats a process of displaying a preview image p-pre on a display section 58a based on the thinned data Dt when the thinned data Dt is transmitted from the radiation imaging apparatus 1, and wherein the control means 22 of the radiation imaging apparatus 1 transmits respective image data D obtained by the respective radiation imaging to the console 58 when a prescribed series of radiation imaging are completed.

Description

  The present invention relates to a radiographic image capturing system and a radiographic image capturing apparatus, and more particularly to a radiographic image capturing apparatus capable of capturing a radiographic image in cooperation with or without cooperation with a radiation generation apparatus.

  A so-called direct type radiographic imaging device that generates electric charges by a detection element in accordance with the dose of irradiated radiation such as X-rays and converts it into an electrical signal, or other radiation such as visible light with a scintillator or the like. 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 apparatus is known as an FPD (Flat Panel Detector), and conventionally formed integrally with a support base (or a bucky apparatus) (see, for example, Patent Document 1). A portable radiographic image capturing apparatus in which an element or the like is stored in a housing and made portable is developed and put into practical use (see, for example, 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 by thin film transistors (hereinafter referred to as TFTs) 8.

  In general, in radiographic imaging, radiation is applied to the radiographic imaging apparatus from a radiation source 52 (see FIGS. 13 and 15 described later) of the radiation generation apparatus 55 in a state through a subject such as the body of the subject. To be done. At that time, by applying the 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 with all the TFTs 8 in the 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, an on-voltage is sequentially applied from the gate driver 15b to each of the lines L1 to Lx of the scanning line 5 to sequentially turn on the TFTs 8 so as to be 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.

  Each image data D read from each radiation detection element 7 is transmitted from the radiation image capturing apparatus to a console 58 (see FIGS. 13 and 15 to be described later), and whether or not the capturing has been performed normally, that is, in the image In order for a radiographer or the like to check whether or not the subject has been photographed and the position of the photographed subject in the image is normal, a preview based on the image data D is usually displayed on the display unit 58a of the console 58. An image is displayed.

  Then, the radiologist or the like looks at the preview image displayed on the display unit 58a of the console 58, determines whether or not imaging has been performed normally, and determines whether or not re-imaging is necessary.

  In this case, if the display of the preview image is slow, the patient who is the subject must wait for that time, and the burden on the patient increases. Therefore, it is required to display the preview image on the display unit 58a of the console 58 as quickly as possible. The preview image may be any image that can be used to determine whether or not shooting has been performed normally, and does not have to display all image data D after performing strict image processing.

  Therefore, when the image data D for the preview image is transmitted from the radiographic apparatus to the console 58, the image data D is thinned out from all the image data D at a predetermined ratio in order to quickly display the preview image. In some cases, the thinned data is generated, and the created thinned data is transmitted to the console 58.

  In this case, the console 58 is configured to display a preview image based on the thinned data on the display unit 58a.

JP-A-9-73144 JP 2006-058124 A JP-A-6-342099

  By the way, as described above, among the image data D read from each radiation detection element 7 of the radiographic image capturing apparatus, only the thinned data is first transmitted to the console 58 to display the preview image. In this case, after the thinning data is transmitted from the radiographic image capturing apparatus, the remaining image data D is transmitted to the console 58.

  Moreover, after transmitting thinning data from the radiographic image capturing apparatus, it corresponds to an offset due to so-called dark charges that are always generated by thermal excitation by heat of each radiation detection element 7 itself, which is superimposed on each image data D. In some cases, the reading process of the offset data O for obtaining the data to be processed, that is, the offset data O is performed. In this case, the offset data O is read from each radiation detection element 7 and then transmitted to the console 58.

  However, as described above, while the remaining image data D is transmitted from the radiographic imaging device or while the offset data O is being acquired by the radiographic imaging device, radiation is applied to the radiographic imaging device. The next imaging performed by irradiation cannot be performed, and the cycle time from the irradiation of the previous imaging to the irradiation of the next imaging becomes long.

  Therefore, for example, in the case of continuously performing imaging on an imaging region such as the chest and abdomen for one patient, if the cycle time becomes longer for each imaging as described above, not only the radiographer but also the patient However, it is necessary to wait until the radiographic image capturing apparatus transmits the remaining image data D or finishes the process of acquiring the offset data O and is ready for the next imaging.

  Therefore, the entire radiographic imaging system including the radiographic imaging device, the radiation generating device 55, the console 58 (see FIGS. 13 and 15 to be described later) and the like is not only convenient for the radiologist but also for the patient. There was a problem that it would be inconvenient.

  The present invention has been made in view of the above problems, and provides a radiographic image capturing system and a radiographic image capturing apparatus capable of performing imaging in a short cycle time even when imaging is performed continuously. For the purpose.

In order to solve the above problems, the radiographic image capturing system and radiographic image capturing apparatus of the present invention include:
In a radiographic imaging system comprising: a radiographic imaging device that acquires image data by radiographic imaging; and a console that includes a display unit that displays a radiographic image.
The radiographic image capturing apparatus includes:
A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; A detector comprising:
Scanning drive means for sequentially applying an on-voltage to each of the scanning lines while switching the scanning lines to which an on-voltage is applied;
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;
Control means for controlling at least the scanning drive means and the readout circuit to perform readout processing of the image data from the radiation detection element;
A communication means for transmitting and receiving signals to and from the console;
With
In a predetermined series of radiographic image capturing, the control means of the radiographic image capturing apparatus reads the image data from the image data read from the radiation detecting elements at a predetermined time each time radiographic image capturing is completed. Thinning out data at a rate to create thinned data and sending it to the console. When the thinned data is transmitted from the radiographic imaging device, the console displays a preview image based on the thinned data on the display unit. Repeat
The control unit of the radiographic image capturing apparatus transmits the image data obtained by radiographic image capturing to the console when the predetermined series of radiographic image capturing is completed.

  According to the radiation image capturing system and the radiation image capturing apparatus of the system of the present invention, during the series of radiation image capturing, only the thinned data is transmitted from the radiation image capturing apparatus to the console, and the series of radiation image capturing After the imaging is completed, each image data obtained by each radiographic imaging is transmitted to the console.

  As described above, since the thinned data is transmitted for each photographing, the amount of data to be transmitted is smaller than that in the case of transmitting all the image data, and the transmission time is shortened. It is possible to display a preview image. Therefore, a radiographer or the like can quickly and accurately determine whether or not re-imaging is necessary.

  In addition, since all image data is not transmitted during a series of imaging, it does not take time to transmit the image data, and a radiographer or the like irradiates radiation at the time of the previous imaging and then the next imaging. Thus, it is possible to shorten the cycle time until radiation is applied.

  Therefore, the radiographer or the like can immediately prepare for the next radiographing after the radiographing is completed, and the radiographic image capturing system can be easily used by the radiographer or the like. Further, the time that the patient waits during imaging is shortened, and the radiographic imaging system can be made convenient for the patient.

It is an external appearance perspective view of the radiographic imaging device concerning this embodiment. It is the external appearance perspective view which looked at the radiographic imaging apparatus of FIG. 1 from the other side. It is sectional drawing which follows the XX line in FIG. 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 showing an example of the method of extracting thinning-out data from image data. (A) It is a figure showing the example of the thinning data extracted from image data, (B) It is the figure which put together the thinning data extracted in (A) notionally into a group. It is a figure which shows the structural example of the radiographic imaging system constructed | assembled in the imaging | photography room etc. It is an external appearance perspective view showing the state to which the connector of the radiographic imaging device and the connector of the Bucky device were connected. It is a figure which shows the structural example of the radiographic imaging system constructed | assembled on the round-trip car. It is a figure which shows the example of imaging | photography order information. It is a figure which shows the example of the selection screen which displays imaging | photography order information. It is a figure which shows the example of the screen on which each icon etc. corresponding to each imaging | photography order information selected were displayed. It is a figure which shows the state by which the preview image was displayed on the position of the icon. It is a figure which shows the state by which the radiographic image was displayed on the position of the icon. It is a timing chart in the reset process for 1 surface. It is a timing chart showing the timing of transmission of the irradiation start signal in a cooperation system, completion | finish of a reset process, transfer to a charge accumulation state, transmission of an interlock release signal, and radiation irradiation. It is a timing chart showing the timing which applies an ON voltage sequentially to each scanning line in a cooperation system. 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 the non-cooperative method. 6 is a timing chart illustrating an example of timing for sequentially applying an on-voltage to each scanning line when the image data reading process is stopped when the start of radiation irradiation is detected in the non-cooperative method. It is the graph which plotted the image data read by the read-out process performed before radiographic image imaging in time series. 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 when leak data read processing and reset processing are alternately performed before radiographic imaging and leak data read processing is performed in a charge accumulation state. FIG. 31 is a timing chart for explaining the timing of applying an ON voltage to each scanning line when leak data is read out in the charge accumulation state in FIG. 30. It is a graph which shows that leak data reduce when irradiation of radiation is completed. FIG. 26 is a timing chart illustrating an example of timing for sequentially applying an ON voltage to each scanning line when the ON time is extended in FIG. 25. 30 is a timing chart showing on / off timings of the charge reset switch, pulse signal, and TFT when the pulse signal transmission interval is increased in FIG. FIG. 24 is a timing chart for explaining that offset data reading processing is performed by repeating the same processing sequence as the series of processing shown in FIG. 23. It is a figure which shows the procedure of the various processes performed with the radiographic imaging apparatus and console in a series of imaging | photography in the conventional case. It is a figure which shows the procedure of the various processes performed with the radiographic imaging apparatus and console in a series of imaging | photography in this embodiment. It is a block diagram showing an example of the equivalent circuit of the radiographic imaging apparatus provided with the electric current detection means.

  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 electric 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 an external perspective view of the radiographic image capturing apparatus according to the present embodiment, and FIG. 2 is an external perspective view of the radiographic image capturing apparatus viewed from the opposite side. FIG. 3 is a sectional view taken along line XX of FIG. As shown in FIGS. 1 to 3, the radiographic image capturing apparatus 1 includes a housing 2 in which a sensor panel SP including a scintillator 3 and a substrate 4 is accommodated.

  As shown in FIG. 1 and FIG. 2, in this embodiment, a hollow rectangular tube-shaped housing body 2A having a radiation incident surface R in the housing 2 is made 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 housing body 2A with lid members 2B and 2C. Instead of forming the casing 2 as such a so-called monocoque type, for example, a so-called lunch box type formed of a front plate and a back plate can be used.

  As shown in FIG. 1, the lid member 2 </ b> B on one side of the housing 2 is configured with a power switch 37, a changeover switch 38, a connector 39, an LED that displays a battery state, an operating state of the radiographic imaging apparatus 1, and the like. The indicator 40 and the like are arranged.

  In this embodiment, the connector 39 transmits image data D or the like to a console 58 (see FIGS. 13 and 15) described later by connecting a cable 51b or the like, for example, as shown in FIG. In addition, it functions as a communication means in the case of a so-called cooperative method in which information and signals are exchanged between the radiation image capturing apparatus 1 and a radiation generation apparatus 55 described later. In addition, the installation position of the connector 39 is not limited to the lid member 2 </ b> B, and can be installed at an appropriate position of the radiographic image capturing apparatus 1.

  Further, as shown in FIG. 2, for example, the radiographic image capturing apparatus 1 and the radiation generating apparatus 55 do not exchange information and signals, and the radiographic image capturing apparatus 1 exchanges information and signals only with the console 58. In the case of the non-cooperation method, an antenna device 41 as a communication unit for performing exchange of information, signals, and the like with the console 58 by a wireless method is provided, for example, on the lid member 2C on the opposite side of the housing 2 or the like. . The antenna device 41 can be provided, for example, by being embedded in the lid member 2C.

  The installation position of the antenna device 41 is not limited to the lid member 2 </ b> C, and the antenna device 41 can be installed at an arbitrary position of the radiographic image capturing apparatus 1. Further, the number of antenna devices 41 to be installed is not limited to one, and a plurality of antenna devices can be provided.

  When radiographic imaging is performed in a non-cooperative manner, the radiographic imaging device 1 is brought to the console 58 after imaging, and a cable (not shown) extending from the console 58 is connected to the connector 39 of the radiographic imaging device 1. It is also possible to perform transmission / reception of information, signals, and the like between the radiation image capturing apparatus 1 and the console 58 by a wired system.

  As shown in FIG. 3, 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 is disposed on the base 31. The PCB substrate 33, the buffer member 34, and the like are attached. Further, a glass substrate 35 for protecting the substrate 4 and the radiation incident surface R of the scintillator 3 is disposed. Moreover, in this embodiment, the buffer material 36 for preventing that they collide between the sensor panel SP and the side surface of the housing | casing 2 is provided.

  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 when receiving radiation, that is, an electromagnetic wave centered on visible light and output. .

  In the present embodiment, the substrate 4 is formed of a glass substrate. As shown in FIG. 4, a plurality of scanning lines 5 and a plurality of signal lines are provided on a surface 4 a of the substrate 4 facing the scintillator 3. 6 are arranged so as to cross each other. In each small region r defined by the plurality of scanning lines 5 and the plurality of signal lines 6 on the surface 4 a of the substrate 4, radiation detection elements 7 are respectively provided.

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

  In the present embodiment, a photodiode is used as the radiation detection element 7, but other than this, for example, a phototransistor or the like can also be used. 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.

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

  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.

  In the present embodiment, as shown in FIG. 4, each scanning line 5, each signal line 6, and connection 10 of the bias line 9 are input / output terminals (also referred to as pads) provided near the edge of the substrate 4. ) 11. As shown in FIG. 6, each input / output terminal 11 has a flexible circuit board (also referred to as “Chip On Film” or the like) on which a chip such as a gate IC 15c constituting a gate driver 15b of a scanning drive unit 15 to be described later is incorporated. .) 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 bias voltage to the second electrode 7 b of each radiation detection element 7 via the connection 10 and each bias line 9. The bias power supply 14 is connected to a control means 22 described later, and the control means 22 controls the bias voltage applied to each radiation detection element 7 from the bias power supply 14.

  As shown in FIGS. 7 and 8, in the present embodiment, the bias power supply 14 supplies the second electrode 7 b of the radiation detection element 7 to the first electrode 7 a side of the radiation detection element 7 as a bias voltage via the bias line 9. A voltage equal to or lower than the voltage applied to (i.e., a so-called reverse bias voltage) is applied.

  The scanning drive means 15 is a power supply circuit 15a that supplies 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.

  The application of the ON voltage from the gate driver 15b of the scanning drive unit 15 to the lines L1 to Lx of the scanning line 5 during the reading process of the image data D from each radiation detecting element 7 will be described later. To do.

  As shown in FIGS. 7 and 8, each signal line 6 is connected to each readout circuit 17 formed 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 reading IC 16. 7 and 8, the correlated double sampling circuit 19 is represented as CDS. In FIG. 8, the analog multiplexer 21 is omitted.

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 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. . Note that the reference potential V ₀ is set to an appropriate value, and in this embodiment, for example, 0 [V] is applied.

  The charge reset switch 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. When each TFT 8 is turned on in the state (and the switch 18e is turned off), electric charges are released from the radiation detection elements 7 to the signal lines 6 through the respective TFTs 8 turned on, The signal passes through the charge reset switch 18c of the amplifier circuit 18, passes through the operational amplifier 18a from the output terminal side of the operational amplifier 18a, is grounded from the non-inverting input terminal, or flows out to the power supply unit 18d.

  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 detecting elements 7 to the signal lines 6 through the TFTs 8 that are turned on, the charges are accumulated in the capacitor 18b 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 by the amplifier circuit 18. Is converted into a charge voltage.

  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 amplification circuit 18 at that time is held, and the charge flowing out from each radiation detection element 7 as described above is accumulated in the capacitor 18b of the amplification circuit 18 and then from the control means 22. When the pulse signal Sp2 is transmitted, the voltage value Vfi output from the amplifier circuit 18 at that time is held.

  When the correlated double sampling circuit 19 holds the voltage value Vfi with the second pulse signal Sp2, the correlated double sampling circuit 19 calculates the difference Vfi−Vin of the voltage value, and uses the calculated difference Vfi−Vin as downstream image data D of the analog value. Output to the side. Then, 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 converted into a digital value by the A / D converter 20. Are converted into image data D, output to the storage means 23 and sequentially stored.

  When one reading process of the image data D is completed, the charge reset switch 18c of the amplifier circuit 18 is turned on (see FIG. 10), and the charge accumulated in the capacitor 18b is discharged, and the same as above. On the other hand, the discharged electric charge passes through the operational amplifier 18a from the output terminal side of the operational amplifier 18a, goes out from the non-inverting input terminal, is grounded, or flows out to the power supply unit 18d.

  The control means 22 includes a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), an input / output interface connected to the bus, an FPGA (Field Programmable Gate Array), or the like (not shown). 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 a DRAM (Dynamic RAM) 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. Further, a connection terminal 25 for charging the battery 24 by supplying power to the battery 24 from a charging device (not shown) is attached to the battery 24.

  As described above, the control unit 22 controls the bias power supply 14 to set or vary the bias voltage applied from the bias power supply 14 to each radiation detection element 7. It is designed to control the operation.

  As will be described in detail later, the control means 22 reads out the image data D and performs the above-described processing from before the radiographic image capturing to the readout processing of the image data D in the cooperation method and the non-cooperation method. When the data is stored in the storage unit 23, the thinned data Dt is generated based on the read image data D and transmitted to the console 58.

  In this case, the thinned data Dt is data obtained by thinning data at a predetermined rate from each image data D as described above. For example, each image corresponding to each radiation detection element 7 arranged in a two-dimensional manner. When data D is arranged, for example, as shown in FIG. 11, it is possible to create image data D for one pixel every 3 × 3 pixels or 4 × 4 pixels. In FIG. 11 and FIG. 12 to be described later, the image data D read from the radiation detection element (m, n) in the m-th row and the n-th column is represented by D (m, n).

  Further, for example, the image data D from each radiation detection element 7 connected to each of the lines L1, L5, L9,... Of the scanning line 5 is connected to each line Ln at a predetermined interval of the scanning line 5. It is also possible to configure so that the image data D from each radiation detection element 7 is extracted and created.

  Specifically, for example, as shown by hatching in FIG. 12A, one line is provided for each line L1 to Lx of a predetermined number (four in the case of FIG. 12A) of scanning lines 5. The scanning line 5 is designated by a ratio, and each image data D (n) read from each radiation detecting element 7 connected to each line L of the designated scanning line 5 is designated as shown in FIG. , M) is set as the thinned data Dt.

  Thus, the control means 22 extracts each image data D of each radiation detection element 7 designated in advance from each image data D read from each radiation detection element 7 as thinning data Dt, The thinned data Dt is transmitted to the console 58 via the connector 39 and the antenna device 41 as communication means.

  FIG. 12B is a diagram showing an image when the thinned data Dt is collected into a group to the last. Actually, the thinned data Dt is created as a group of data on the storage means 23, for example. Instead, only the thinned data Dt is read and extracted from the image data D stored in the storage means 23, and the thinned data Dt is immediately transmitted to the console 58 every time it is read from the storage means 23.

  In the present invention, after the thinned data Dt is transmitted, the remaining image data D other than the thinned data Dt is transmitted from the radiographic image capturing apparatus 1 to the console 58. The configuration and the like of the photographing system 50 will be described later.

[Radiation imaging system]
Next, the radiographic imaging system according to the present embodiment will be described. FIG. 13 is a diagram illustrating a configuration of a radiographic image capturing system according to the present embodiment.

  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. 13 shows a case where a bucky device 51A for standing shooting and a bucky device 51B for standing shooting are installed as the bucky device 51. For example, a bucky device for standing shooting is shown. Only 51A or only the bucky device 51B for lying position photography may be provided.

  In the present embodiment, as shown in FIG. 14, the connector 39 of the radiographic image capturing apparatus 1 and the connector 51 c provided at the tip of the cable 51 b extending from the bucky device 51 are connected, and the radiographic image capturing apparatus. 1 is loaded into the bucky device 51. It is also possible to provide a connector 51c in the cassette holding part 51a so that the connector 39 and the connector 51c are automatically connected when the radiation image capturing apparatus 1 is loaded. Composed.

  In the present embodiment, the bucky device 51 supplies power from the bucky device 51 to the radiographic imaging device 1 when the connector 51c and the connector 39 of the radiographic imaging device 1 are connected, which will be described later. Transmission / reception of image data D, signals, and the like to / from the console 58 is performed in a wired manner via the cable 51b of the bucky device 51 and a repeater 54 described later. It is also possible to configure transmission / reception of image data D and signals to / from the console 58 via the antenna device 41 in a wireless manner.

  Further, in the present embodiment, when the radiographic image capturing apparatus 1 is used in the Bucky apparatus 51 in the photographing room R1, it exchanges signals with the radiation generating apparatus 55, which will be described later, and the radiation generating apparatus 55. Radiographic imaging is performed in a cooperative manner in which radiography is performed in cooperation with the radiography. In this case, the exchange of signals with the radiation generation device 55 is performed via the cable 51b of the Bucky device 51 or a repeater 54 described later. It has become.

  As shown in FIG. 13, the imaging room R1 is provided with at least one radiation source 52A for irradiating the radiation image capturing apparatus 1 loaded in the Bucky apparatus 51 via the subject. 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 an access point, a base station, etc.) 54 for relaying communication between each device in the imaging room R1 and each device outside the imaging room R1. ing. In the present embodiment, the repeater 54 is provided with a wireless antenna 53 so that the radiographic image capturing apparatus 1 can transmit and receive image data D, signals, and the like in a wireless manner. In the present embodiment, the above-described Bucky devices 51A and 51B and the repeater 54 are connected by cables or the like.

  The relay 54 is connected to the radiation generator 55 and the console 58, and the relay 54 transmits a signal for LAN communication transmitted to the radiation generator 55 from the radiographic imaging device 1, the console 58, and the like. A converter (not shown) that converts the signal into a signal for the radiation generator 55 and the reverse conversion is incorporated.

  In the present embodiment, the front room (also referred to as the operation room) R2 is provided with an operation console 57 of the radiation generating device 55. The operation console 57 is operated by an operator such as a radiation engineer to generate radiation. An exposure switch 56 is provided for instructing the apparatus 55 to start radiation irradiation. In this embodiment, an operator such as a radiologist operates the exposure switch 56 twice so that radiation is emitted from the radiation source 52.

  Specifically, when the operator performs the first operation on the exposure switch 56, an activation signal is transmitted from the console 57 to the radiation generator 55. The radiation generator 55 When the activation signal is received, the radiation source 52A is activated. When the second operation is performed on the exposure switch 56, an irradiation start signal is transmitted from the console 57 to the radiation generator 55.

  As will be described later, when imaging is performed in a cooperative manner, this irradiation start signal is also transmitted to the radiographic image capturing apparatus 1 via the repeater 54. As will be described later, when an interlock release signal is transmitted from the radiographic imaging apparatus 1 via the relay 54, the radiation generation apparatus 55 emits radiation from the radiation source 52.

  In addition to this, the radiation generating device 55 moves the radiation source 52 to a predetermined position so that the radiation image capturing device 1 loaded in the designated bucky device 51 can be appropriately irradiated with radiation, or the radiation direction thereof. The radiation source 52 is adjusted so that a diaphragm, a collimator, etc. (not shown) are adjusted so that the radiation is irradiated in a predetermined region of the radiographic image capturing apparatus 1, or an appropriate dose of radiation is irradiated. Various controls such as adjustment of the radiation source 52 are performed on the radiation source 52.

  In addition, the radiation generation device 55 ends the radiation irradiation from the radiation source 52 when a set time has elapsed from the start of the radiation irradiation.

  On the other hand, as shown in FIG. 15, 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 between the body and the patient's body.

  When the radiographic image capturing apparatus 1 is used in this way, for example, as shown in FIG. 14, using a cable connected to the connector 39 of the radiographic image capturing apparatus 1 often obstructs the cable. In the embodiment, when the radiographic image capturing apparatus 1 is used alone, it is used without connecting a cable to the connector 39.

  Therefore, in this case, since the radiographic imaging device 1 cannot receive power supply from an external device, the control unit 22 of the radiographic imaging device 1 receives each functional unit from the battery 24 (see FIG. 7). Electric power is supplied to operate necessary functional units.

  Further, when the radiographic image capturing apparatus 1 is used in a hospital room R3 or the like, the radiation generator 55 or the radiation source 52A installed in the above-described image capturing room R1 cannot be brought into the hospital room R3. The portable radiation generating device 55 is brought into the hospital room R3, for example, by being mounted on the roundabout wheel 71.

  In this case, the radiation 52P of the portable radiation generator 55 is configured to be able to irradiate radiation in an arbitrary direction. The radiation imaging apparatus 1 inserted between the bed B and the patient's body or applied to the patient's body can be irradiated with radiation from an appropriate distance or direction. Yes.

  As shown in FIG. 13, the radiographic image capturing apparatus 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.

  Further, when the radiographic imaging apparatus 1 is used in the hospital room R3 or the imaging room R1 as described above without connecting the cable to the connector 39, the portable radiation generator 55 (or the imaging room in the above case). It is not possible to exchange signals with the R1 radiation generator 55).

  Therefore, in such a case, the radiographic imaging device 1 performs imaging in a non-cooperative manner that does not exchange signals with the radiation generation device 55. That is, the radiation image capturing apparatus 1 itself irradiates radiation without receiving the irradiation start signal as described above from the radiation generating apparatus 55 or transmitting the interlock release signal from the radiation image capturing apparatus 1. It is necessary to detect the start of the radiographing and the like to perform radiographic imaging.

  The control configuration for that will be described later. For example, when radiographing is performed in the hospital room R3 or the like, the radiographic imaging device 1 is brought to the console 58 where image processing for generating a final radiographic image can be performed after imaging, for example. As described above, for example, as shown in FIG. 14, it is possible to connect the cable of the console 58 to the connector 39 of the radiographic image capturing apparatus 1 and transmit the image data D and the like as described above.

  However, at least the preview image based on the thinning data Dt is displayed on the console 58 mounted on the round wheel 71 by transmitting the thinning data Dt from the radiographic image capturing apparatus 1 to the console 58 mounted on the round wheel 71. Done.

  As shown in FIG. 13, 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 or the front room R2, in a separate room, or the like, and the installation location of the console 58 is appropriately determined.

  Further, the console 58 is provided with a display unit 58a configured with a CRT (Cathode Ray Tube), an LCD (Liquid Crystal Display), or the like, and a memory configured with an HDD (Hard Disk Drive) or the like. Means 59 are connected or built in.

  In the present embodiment, when the thinning data Dt, the image data D, and the like are transmitted from the radiation image capturing apparatus 1, the console 58 displays a preview image on the display unit 58a based on the data. Hereinafter, this point will be described.

  Hereinafter, generation of a final radiographic image in the console 58 will also be described. However, in the console 58 of the radiographic imaging system 50 constructed on the round wheel 71 shown in FIG. 15, a preview on the display unit 58a is displayed. It is also possible to configure so that image display processing is performed, and the final radiation image is generated by another console 58 or an image processing apparatus having a generation processing function.

  Prior to imaging, the console 58 performs imaging from a non-illustrated HIS (Hospital Information System) or RIS (Radiology Information System) connected to a network (not illustrated) by the operation of a radiographer or the like. Necessary information such as order information is obtained.

  The imaging order information is set by specifying at least a patient, an imaging region, and the like as a subject.

  Specifically, as shown in FIG. 16, the imaging order information includes “patient ID” P2, “patient name” P3, “gender” P4, “age” P5, “clinical department” P6 as patient information. , “Imaging region” P7, “imaging direction” P8, and the like.

  Further, as shown in FIG. 16, it is also possible to designate a “bucket ID” P9 representing the bucky device 51 to be used, a “cassette ID” P10 of the cassette to be used, and the like. Then, “shooting order ID” P1 is automatically assigned to each shooting order information in the order in which shooting orders are registered.

  When obtaining the shooting order information, the console 58 displays a list of each shooting order information on the display unit 58a as a selection screen H1, as shown in FIG. In the present embodiment, a shooting order information display field h11, a selection button h12, a determination button h13, and a return button h14 are displayed on the selection screen H1.

  Then, for example, when the radiographer clicks the selection button h12, selects each radiographing order information and clicks the decision button h13, the console 58 is displayed on the display unit 58a, for example, a screen H2 as shown in FIG. Is displayed.

  As shown in FIG. 18, each icon I corresponding to each shooting order information is displayed on the screen H2, and a preview image p_pre displayed at the position of the icon I as described later is displayed below each icon I. An “OK” button that is clicked when it is determined that re-imaging is unnecessary by viewing a radiologist or the like, and an “NG” button that is clicked when it is determined that re-imaging is necessary are displayed.

  In this case, as will be described later, when the radiologist or the like designates the icon I on the screen H2 of the console 58, the “imaging part” P7 (see FIGS. 16 and 17) of the imaging order information corresponding to the designated icon I. Information) is transmitted to the radiation generation device 55, and the radiation generation device 55 adjusts the radiation dose and the like to be irradiated from the radiation source 52 based on the information on the imaging region and the like.

  In FIG. 18, a display for setting irradiation conditions is displayed on the right side of the screen H <b> 2 so that a radiographer or the like can finely adjust the dose of radiation irradiated from the radiation source 52 on the screen H <b> 2 of the console 58. Ia is displayed. Then, by clicking the “+” button or the “−” button for each item on the display Ia, the irradiation conditions such as the tube voltage, tube current, and irradiation time of the radiation source 52 of the radiation generator 55 are changed and set. Can be done.

  On the other hand, in the present embodiment, each of the icons I1 to I4 is displayed so that any one icon I (icon I2 in the case of FIG. 18) is conspicuously displayed. Shooting based on shooting order information corresponding to I is performed.

  In this embodiment, the console 58 automatically focuses the icon I satisfying a predetermined condition. However, when a radiographer or the like wants to perform imaging based on other imaging order information, The focus can be changed by clicking and operating another icon I corresponding to the shooting order information.

  In the present embodiment, the console 58 transmits a signal or the like to the radiation generator 55 in the imaging room R so that imaging based on imaging order information corresponding to the focused icon I is performed. Then, the radiation generating device 55 is activated with the predetermined radiation source 52, and the radiation source 52 is irradiated with an appropriate dose corresponding to the imaging region specified by the imaging order information. Control such as supplying a tube current and moving the radiation source 52 is performed.

  Further, as described above, when the tube voltage, the tube current, or the like is changed and set on the screen H2 (see FIG. 18), the console 58 transmits the information to the radiation generation device 55 to transmit the radiation. The generator 55 is controlled to change the tube voltage supplied to the radiation source 52 or the like.

  As described above, a radiation engineer or the like can also be configured to directly adjust the radiation generator 55 and the radiation source 52.

  In addition, on the left side of the screen H2, the imaging part designated by the imaging order information corresponding to the icon I displayed in focus is displayed on the human body model Ib which is displayed so that the radiologist can understand at a glance. It has become so.

  On the other hand, when radiographic image capturing based on radiographing order information corresponding to the icon I displayed in focus is performed, as described above, the thinning data Dt of each radiation detection element 7 is transmitted from the radiographic image capturing apparatus 1. It will be.

  In this embodiment, when the thinning data Dt is transmitted from the radiation image capturing apparatus 1, the console 58 focuses the preview image p_pre on the basis of the transmitted thinning data Dt as shown in FIG. It is displayed at the position of the original icon I2. Note that the preview image p_pre may be enlarged and displayed on the screen H2 so that a radiographer or the like can easily view the preview image p_pre.

  Then, when a radiographer or the like who has viewed the preview image p_pre clicks the “OK” button, the console 58 corresponds the thinning data Dt transmitted from the radiographic image capturing apparatus 1 to the imaging order information corresponding to the icon I2. It comes to save it.

  Note that, when a radiologist or the like who has viewed the preview image p_pre clicks the “NG” button, re-imaging is performed, and thus the thinning data Dt is not necessary. Therefore, the console 58 cancels the association of the thinning data Dt with the photographing order information and deletes the thinning data Dt.

  On the other hand, when the final radiation image p is generated on the console 58, the console 58 transmits the remaining image data D from the radiation image capturing apparatus 1 as will be described later. At this point, all the image data D read from each radiation detection element 7 of the radiation image capturing apparatus 1 is restored by combining the thinned data Dt already received and the remaining image data D.

  Then, a gain correction value, defective pixel data, and the like related to the radiographic image capturing apparatus 1 used for the imaging, which are stored in the storage unit 59, are read, and gain correction and offset correction are performed on the image data D based on them. The final radiation image p is generated by performing processing such as defect pixel correction and gradation processing according to the imaging region.

  In this embodiment, when generating the radiation image p, the console 58 displays the generated radiation image p (in this case, the radiation image p2) at the position of the original icon I2, as shown in FIG. It has become.

  When a radiographer or the like who has seen the radiation image p determines that the generated radiation image p is normal and clicks an “OK” button, the console 58 determines the radiation image p, and the radiation image p Is stored in the storage means 59 in association with the imaging order information.

[Processing when shooting in linked mode]
Next, in the cooperative system in which the radiographic image capturing apparatus 1 and the radiation generating apparatus 55 exchange signals and the radiographic image capturing apparatus 1 and the radiation generating apparatus 55 perform radiographic image capturing in cooperation with the radiographic image capturing apparatus 1. A processing configuration from before radiographic image capturing to image data D readout processing will be described.

  For example, as illustrated in FIG. 14, the imaging by the cooperation method is illustrated in FIG. 13 in a state where the connector 39 of the radiographic image capturing apparatus 1 and the connector 51 c of the cable 51 b provided in the bucky apparatus 51 are connected. As described above, it is performed when the radiographic image capturing apparatus 1 is loaded in the Bucky apparatus 51 and radiographic image capturing is performed.

  In this embodiment, when radiographic imaging is performed in a cooperative manner, the control unit 22 of the radiographic imaging apparatus 1 first performs reset processing of each radiation detection element 7 before radiographic imaging. .

  In the reset process of each radiation detection element 7, for example, as shown in FIG. 21, an on-voltage is applied to each line L <b> 1 to Lx of the scanning line 5 from the gate driver 15 b (see FIG. 8) of the scanning drive unit 15. Then, an ON voltage is applied to the gate electrode 8 g of each TFT 8 to turn on the TFT 8, and extra charges are discharged from each radiation detection element 7 to each signal line 6.

  Then, as shown in FIG. 21, the scanning lines 5 to which the on-voltage is applied are sequentially switched, the on-voltage is sequentially applied to the lines L1 to Lx of the scanning line 5, and the reset process of each radiation detection element 7 is repeated. . In this way, the control means 22 repeats the reset process Rm for one surface, which is performed by sequentially applying the ON voltage from the first line L1 to the last line Lx of the scanning line 5.

  In this case, when the reset process Rm for one surface is repeated a predetermined number of times, the reset process of each radiation detection element 7 is finished, and thereafter, the off voltage is applied to all the lines L1 to Lx of the scanning line 5. However, it is also possible to configure to wait for radiation irradiation in a state where all TFTs 8 are turned off. Further, from the viewpoint of performing imaging in a state where there is less excess charge remaining in each radiation detection element 7, it is possible to repeat the reset processing of each radiation detection element 7 until immediately before the start of radiation irradiation. is there.

  Then, as shown in FIG. 22, during the reset process Rm for one surface, the exposure switch 56 is operated on the radiation generation device 55 side as described above, and the radiation image capturing device 1 from the radiation generation device 55 is operated. When the irradiation start signal is transmitted, the control means 22 of the radiographic image capturing apparatus 1 sets each radiation at the time when the reset process Rm for one surface performed when the irradiation start signal is transmitted is completed. The reset process of the detection element 7 is terminated.

  Then, an off voltage is applied from the scanning drive means 15 to all the lines L1 to Lx of the scanning line 5 to turn off all the TFTs 8, and the charges generated in each radiation detecting element 7 due to the irradiation of radiation are transferred to each radiation detecting element. 7 is shifted to a charge accumulation state to be accumulated in the inside.

  Further, the control means 22 transmits an interlock release signal to the radiation generator 55 when the reset process Rm for one surface is completed as described above. When receiving the interlock release signal from the radiographic image capturing apparatus 1 via the relay 54, the radiation generation apparatus 55 causes the radiation source 52 to emit radiation.

  In this embodiment, the control means 22 of the radiographic image capturing apparatus 1 turns on each line L1 to Lx of the scanning line 5 as shown in FIG. A voltage is sequentially applied to read the image data D from each radiation detection element 7. In addition, the oblique line in FIG. 23 represents that the radiation was irradiated in the period.

  In this case, when the irradiation of the radiation from the radiation source 52 is finished, the radiation generator 55 is configured to transmit an end signal to the radiographic image capturing device 1, and the radiographic image capturing device 1 outputs the end signal. It is also possible to configure to shift from the charge accumulation state to the reading process of the image data D as soon as it is received.

  Further, the radiation imaging apparatus 1 is configured so that the radiation dose can be measured by the radiation imaging apparatus 1, and radiation irradiation is terminated from the radiation imaging apparatus 1 to the radiation generating apparatus 55 when a predetermined dose of radiation is irradiated. And after the irradiation of radiation from the radiation source 52 is finished, the readout processing of the image data D from each radiation detection element 7 in the radiation image capturing apparatus 1 is started. It is also possible to do.

  If it is configured to transmit an end signal from the radiation generation device 55, or configured to instruct the radiation generation device 55 to end the irradiation from the radiographic imaging device 1 when a predetermined dose of radiation is irradiated, The time for which the accumulation state continues is shortened, and the reading process of the image data D can be started earlier.

[Processing when shooting in unlinked mode]
Next, the radiation image capturing apparatus 1 and the radiation generating apparatus 55 are used, as shown in FIG. 15, in which the radiation image capturing apparatus 1 described above is used in a single state without being loaded into the Bucky apparatus 51 and performs radiation image capturing. In the non-cooperative method in which the radiographic imaging device 1 detects the start of radiation irradiation by itself and performs radiographic imaging without exchanging signals, the processing performed by the radiographic imaging device 1 will be described.

  As described above, for example, the following two detection methods can be adopted as a method of detecting radiation irradiation by the radiographic imaging apparatus 1 itself using each function unit already provided in the apparatus.

[Detection method 1]
For example, as in the case of the above-described cooperation method, instead of configuring to perform reset processing (see FIG. 21 and the like) of each radiation detection element 7 before the radiation image capturing apparatus 1 is irradiated with radiation in radiation image capturing. In addition, as shown in FIG. 24, before radiographic imaging, the on-voltage is sequentially applied from the gate driver 15b of the scanning driving unit 15 to each of the lines L1 to Lx of the scanning line 5, and the image from each radiation detecting element 7 is displayed. The data d can be read repeatedly.

  In addition, the image data read out in the read-out process before radiographic imaging is hereinafter referred to as image data d, in distinction from the image data D as the main image performed immediately after imaging. In FIG. 24, one frame is a process of reading image data d from each radiation detection element 7 for one surface arranged in a two-dimensional manner on the detection unit P (see FIGS. 4 and 7). A period.

  Further, on / off of the charge reset switch 18c of the amplifier circuit 18 of the read circuit 17 and the transmission of the pulse signals Sp1 and Sp2 to the correlated double sampling circuit 19 in the read processing of the image data d are shown in FIG. This is performed in the same manner as the processing for reading out the image data D.

  The reading process of the image data d before radiographic imaging is a process for detecting radiation irradiation by the radiographic imaging apparatus 1 itself as will be described below. It also serves as a reset process for each radiation detection element 7 for removing charges such as charges from the radiation detection elements 7.

  As described above, when the reading process of the image data d is performed before the radiographic image capturing, as shown in FIG. 25, when radiation irradiation to the radiographic image capturing apparatus 1 is started, the data is read at that time. The image data d (in FIG. 25, the image data d read by applying the ON voltage to the line Ln of the scanning line 5) is more than the image data d read before that, as shown in FIG. It becomes a significantly large value (see time t1 in FIG. 26).

  Therefore, the control unit 22 is configured to monitor the image data d read in the reading process before radiographic image capturing, and the read image data d is set in advance as shown in FIG. 26, for example. When the threshold value dth is exceeded, it can be configured to detect the start of radiation irradiation.

  In this case, when the control means 22 detects that the irradiation of radiation has started as described above, it applies an on-voltage to each scanning line 5 at that time as shown in FIG. Then, the gate driver 15b applies an off voltage to all the lines L1 to Lx of the scanning line 5 to turn off the TFTs 8 so that the charges generated in the radiation detecting elements 7 due to the irradiation of the radiation A transition is made to a charge storage state to be stored in the detection element 7.

  Then, after a predetermined time has elapsed since the start of radiation irradiation was detected, the control means 22 detects the start of radiation irradiation in the reading process of the image data d before the radiographic image capture, or immediately before that. The scanning line 5 to which the ON voltage is to be applied next to the scanning line 5 to which the ON voltage is applied (in the case of FIG. 25, the line Ln + 1 of the scanning line 5) is to be applied (in the case of FIG. 25, the line Ln + 1 of the scanning line 5). The application of the on-voltage is started, and the on-voltage is sequentially applied to each scanning line 5 so as to perform the reading process of the image data D as the main image.

  In FIG. 25, the read processing of the image data D as the main image is performed by changing the on-voltage from the line Ln + 1 next to the line Ln of the scanning line 5 to which the on-voltage is applied when the start of radiation irradiation is detected. Although the case where the application is started is shown, for example, it is possible to start the application of the on-voltage from the first line L1 or the like of the scanning line 5 and perform the reading process of the image data D.

[Detection method 2]
Further, as in the detection method 1 described above, instead of configuring to read out the image data d from each radiation detection element 7 before radiographic imaging, the leak data dleak is read out before radiographic imaging. It is also possible to repeat the above.

  Here, as shown in FIG. 27, the leak 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.

  Then, in the reading process of the leak data dleak, as shown in FIG. 28, each reading circuit is supplied from the control means 22 in a state where each TFT 8 is turned off by applying an off voltage to each line L1 to Lx of the scanning line 5. Pulse signals Sp1 and Sp2 are transmitted to 17 correlated double sampling circuits 19 (see CDS in FIGS. 7 and 8).

  As in the case of the reading process of the image data d, the correlated double sampling circuit 19 holds the voltage value Vin output from the amplifier circuit 18 at that time when the pulse signal Sp1 is transmitted from the control means 22. . Then, the charge q leaked from each radiation detection element 7 is accumulated in the capacitor 18b of the amplifier circuit 18 via each TFT 8, the voltage value output from the amplifier circuit 18 rises, 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.

  However, if only the reading process of the leak data dleak is repeatedly performed, each TFT 8 remains off, 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.

  It should be noted that, instead of configuring the readout process of the leak data dleak and the reset process of each radiation detection element 7 alternately, illustration is omitted, but the charge remaining in each radiation detection element 7 is discharged. It is also possible to configure so that the reading process of the leak data dleak and the reading process of the image data d from each radiation detection element 7 are alternately performed.

  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. The charge q (see FIG. 27) leaking from each radiation detection element 7 via each TFT 8 increases.

  Therefore, as shown in FIG. 30, leak data dleak read at that time (in FIG. 30, in the fourth read process after the on-voltage is applied to the line L4 of the scanning line 5 and the reset process is performed). Although the illustration of the leaked leak data dleak) is omitted, the value is larger than the leaked data bleak read before that, as in FIG. 26 in the case of the image data d. In FIG. 30, “R” represents a reset process for each radiation detection element 7, and “L” represents a read process for leak data dleak.

  Therefore, the control unit 22 is configured to monitor the leak data dleak read out in the process of reading out the leak data dleak before radiographic imaging, and the read out leak data dleak is, for example, a predetermined threshold value set in advance. It can be configured to detect that radiation irradiation has started at a time exceeding

  In this case, when the control means 22 detects that the irradiation of radiation has started as described above, it applies an on-voltage to each scanning line 5 at that time as shown in FIG. Then, the gate driver 15b applies an off voltage to all the lines L1 to Lx of the scanning line 5 to turn off the TFTs 8 so that the charges generated in the radiation detecting elements 7 due to the irradiation of the radiation A transition is made to a charge storage state to be stored in the detection element 7.

  Then, after a predetermined time has elapsed since the start of radiation irradiation was detected, the control means 22 detects the start of radiation irradiation in the reading process of the image data d before the radiographic image capture, or immediately before that. Is turned on from the scanning line 5 to which the ON voltage is to be applied next (line L5 of the scanning line 5 in FIG. 30) to the scanning line 5 to which the ON voltage is applied (in the case of FIG. 30, the line L4 of the scanning line 5). Application of a voltage is started, and an ON voltage is sequentially applied to each scanning line 5 to perform a reading process of image data D as a main image.

  Even in the case shown in FIG. 30, it is possible to configure that the reading process of the image data D as the main image is performed by starting the application of the on-voltage from the first line L1 of the scanning line 5, for example. It is.

[Detection of radiation exposure completion]
Further, as shown in FIG. 30, after detecting the start of radiation irradiation, the reset process of each radiation detection element 7 performed by sequentially applying the ON voltage to each scanning line 5 is stopped and the charge is accumulated. At this time, as shown in FIG. 31, in the charge accumulation state, the readout process of the leak data dleak performed by applying the off voltage to each scanning line 5 is continued, so that the radiographic image is obtained. It is also possible to configure so as to detect the end of radiation irradiation on the imaging apparatus 1.

  If the reading process of the leak data dleak is continued after the start of the irradiation of the radiation, since the irradiation of the radiation has already started in the charge accumulation state, the read leak data dleak is large as shown in FIG. Although the value is set, the leakage data dleak returns to the original small value when the irradiation of the radiation image capturing apparatus 1 is completed.

  For this reason, for example, it is possible to detect that the radiation irradiation has ended when the leak data dleak becomes a value equal to or smaller than the threshold dleak_th at time t2. Note that the threshold value dleak_th in this case may be the same value as the threshold value when detecting the start of radiation irradiation by the detection method 2 described above, or may be set as a different value.

  Further, FIG. 32 shows a case where the leak data dleak is continuously read out after the end of radiation irradiation is detected at time t2, and the leak data dleak is read out. When the end of radiation irradiation is detected, the reading process of the leak data dleak is stopped.

  As shown in FIG. 32, when the leak data dleak becomes a value equal to or smaller than the threshold dleak_th and it is detected that the radiation irradiation has ended (see “A” in FIG. 31), this corresponds to the time t2 in FIG. ), The sequential application of the ON voltage to each scanning line 5 is started, and the reading process of the image data D as the main image can be started.

  If comprised in this way, as shown in FIG. 31, it will become possible to start the read-out process of the image data D immediately after detecting the completion | finish of irradiation of a radiation, and the process after the read-out process of the image data D There is an advantage that it is possible to perform the operation at an early stage.

[Detection sensitivity in non-cooperative system]
As described above, in the non-cooperative method (detection methods 1 and 2), the radiographic imaging device 1 does not receive information regarding radiation irradiation from the radiation generation device 55 side, and thus can detect the start of radiation irradiation by itself. Although necessary, since the radiation dose applied to the radiographic imaging apparatus 1 may be small, it is desirable to increase the detection sensitivity at the start of radiation irradiation.

  For example, in the case of the detection method 1 described above, on / off of the charge reset switch 18c of the amplification circuit 18 of the readout circuit 17 in the readout process of the image data d, and the pulse signals Sp1, Sp2 to the correlated double sampling circuit 19 The transmission and the like are basically performed in the same manner as the processing in the reading process of the image data D shown in FIG.

  However, at this time, for example, as shown in FIG. 33, the time T during which the on-voltage is applied to the line Ln of the scanning line 5, that is, the voltage to be applied after the application of the on-voltage to the line Ln of the scanning line 5 is started is turned off. A time T until switching to the voltage (hereinafter, this time is referred to as an ON time T) is configured to be long.

  By increasing the on-time T in this way, the amount of charge flowing from the radiation detection element 7 to the readout circuit 17 via the TFT 8 during the long on-time T increases. Therefore, it is possible to increase the value of the image data d read out in one reading process of the image data d, and it is possible to improve the detection sensitivity at the start of radiation irradiation.

  In the case of the detection method 2 described above, for example, the transmission interval τ of the pulse signals Sp1 and Sp2 transmitted twice to the correlated double sampling circuit 19 of the readout circuit 17 shown in FIG. 29 is as shown in FIG. By configuring the length to be longer, the amount of charge leaking from the radiation detection element 7 via the TFT 8 and flowing into the readout circuit 17 increases.

  For this reason, the value of the leak data dleak read out in one leak data dleak read process can be increased, and in this case as well, the detection sensitivity at the start of radiation irradiation can be improved. .

  As described above, the irradiation time is started by increasing the ON time T (see FIG. 33) and the like in the detection method 1, and by increasing the transmission interval τ (see FIG. 34) of the pulse signals Sp1 and Sp2 in the detection method 2. Therefore, even when a relatively small dose of radiation is irradiated to the radiation image capturing apparatus 1, it is possible to accurately detect the start of radiation irradiation.

[Offset data acquisition processing]
On the other hand, both in the case of the cooperative method shown in FIG. 23 and in the case of the non-cooperative method shown in FIG. 25 (detection method 1), FIG. Therefore, charges generated in each radiation detection element 7 due to radiation irradiation are accumulated in each radiation detection element 7.

  However, at this time, as described above, since the so-called dark charges are always generated in each radiation detection element 7 due to thermal excitation by the heat of each radiation detection element 7 itself, the dark charge is also detected at the same time. Accumulated in the element 7.

For this reason, in the image data D read out by the reading process, dark data is used together with useful data (hereinafter referred to as true image data D ^* ) caused by charges generated in each radiation detection element 7 due to radiation irradiation. The data corresponding to the offset due to, that is, the offset is also included.

Therefore, as described above, when the final radiation image p (see FIG. 20) is generated by performing image processing on the image data D with the console 58, the image data D read from each radiation detection element 7 is used. Obtain offset data O corresponding to the offset due to the dark charge contained in the image data D, which is necessary for calculating the true image data D ^* by subtracting the offset due to the dark charge. It is necessary to do.

  For example, in the case of the cooperation method shown in FIG. 23, in order to detect this offset data O, the control means 22 of the radiographic image capturing apparatus 1 performs processing as shown in FIG. After the image is taken and the image data D is read out, as shown in FIG. 35, the same processing sequence as the series of processes shown in FIG. 23 is repeated to perform the offset data O reading process.

  In other words, the scanning lines 5 are turned on to the lines L1 to Lx from the reset processing of each radiation detection element 7 before radiographic imaging until the readout processing of the image data D as the main image through the charge accumulation state. After sequentially applying an ON voltage to each of the lines L1 to Lx of the scanning line 5 at the same timing as the voltage application timing, the radiation detection element 7 is reset as many times as necessary, and then the charge accumulation state is changed. Then, the offset data O is read out.

  As shown in FIG. 35, in the process of acquiring the offset data O, the radiation image capturing apparatus 1 is not irradiated with radiation after resetting the radiation detection elements 7 as many times as necessary. 23, the radiation image capturing apparatus 1 is left for the same time as the charge accumulation state shown in FIG. 23 to accumulate charges (that is, dark charges in this case) in each radiation detection element 7, and then the image data D is read out. The offset data O is read in the same manner as the processing.

  Further, the reset processing of each radiation detection element 7 performed before the offset data O readout processing is performed for one surface for the same number of times as the reset processing Rm for one surface performed before the readout processing of the image data D. There is no need to perform the process Rm, and the reset process Rm for one surface may be repeated as many times as necessary. It is also possible to configure so that the reset process Rm for one surface is performed only once.

  In the case of the non-cooperative method shown in FIG. 25 (detection method 1), FIG. 30 or the like (detection method 2), the control means 22 of the radiographic image capturing apparatus 1 is similarly as shown in FIG. 25 or FIG. The processing sequence is the same as the series of processing shown in FIG. 25, FIG. 30 and the like after performing radiographic image capturing, reading out the image data D, resetting each radiation detecting element 7 as many times as necessary. To repeat the process of reading the offset data O.

  The offset data O read from each radiation detection element 7 is included in the time when the TFT 8 is in the OFF state including the charge accumulation state (hereinafter referred to as effective accumulation time), that is, before the charge accumulation state. The amount of dark charge accumulated in each radiation detection element 7 between the time when the TFT 8 is finally turned on by the reset processing of 7 and the time between the charge accumulation state and the on state by the readout processing caused by.

  However, it is known that when the effective accumulation time changes, the value of the offset data O to be read does not necessarily increase in proportion to the effective accumulation time.

  However, as described above, the offset data O acquisition process is configured to be repeated from the process before radiographic image capturing to the image data D read process, so that at least the effective accumulation for each scanning line 5 is performed. The time is the same in the reading process of the image data D and the acquisition process of the offset data O. Therefore, it is possible to make the offset value caused by the dark charge included in the image data D and the value of the offset data O acquired by the offset data O acquisition process the same value.

Therefore, by subtracting the offset data O from the image data D in the image processing of the console 58, only the charges generated in each radiation detection element 7 by irradiation of radiation (that is, true charges not including dark charges) are obtained. It is possible to accurately calculate the resulting true image data D ^* .

  As described above, in the present embodiment, when the detection method 1 or the detection method 2 is adopted and shooting is performed in a non-cooperative manner, the same processing sequence as the series of processing illustrated in FIGS. 25 and 30 is performed. It is configured so that the offset data O is read repeatedly. In that case, as described above, the radiation image capturing apparatus 1 is not irradiated with radiation in the reading process of the offset data O. Therefore, it is not necessary to detect the start of radiation irradiation.

  For this reason, in the present embodiment, after the reading process of the image data D as the main image and before the reading process of the offset data O, the control unit 22 starts radiation irradiation based on the image data d and the leak data dleak as described above. The detection process is not performed.

  At that time, after the reading process of the image data D as the main image and before the reading process of the offset data O, the detection process of the irradiation start of the radiation is not performed as described above, but the image data d and the leak data dleak are not performed. The read operation can be performed.

  With this configuration, the same processing sequence as the series of processes up to the reading process of the image data D as the main image is performed except that the control unit 22 does not perform the detection process before the reading process of the offset data O. It becomes possible to repeatedly read the offset data O.

  For this reason, the functional units such as the control unit 22 and the reading circuit 17 are exactly the same as the operations in the reading process of the image data D as the main image, except that the control unit 22 does not perform the detection process in the reading process of the offset data O. By performing the operation, it becomes possible to read the offset data O. Therefore, there is a merit that the control configuration for reading the offset data O can be constructed very easily by using the control configuration for operating each functional unit during the reading processing of the image data D. .

  Further, after the reading process of the image data D as the main image and before the reading process of the offset data O, the detection process of the start of radiation irradiation is not performed as described above, but the reading of the image data d and the leak data dleak is also performed. It is also possible to configure so that no operation is performed.

  For example, in the case of the detection method 1, after the reading process of the image data D as the main image and before the reading process of the offset data O, each scanning line 5 is read at the same timing as the reading process of the image data d before the radiographic image capturing. It is also possible to apply a turn-on voltage to the lines L1 to Lx sequentially, but to perform a reset process for each radiation detection element 7 without causing each readout circuit 17 to perform a readout operation.

  Further, for example, in the case of the detection method 2, after the read processing of the image data D as the main image and before the read processing of the offset data O, the reset processing of each radiation detection element 7 performed alternately with the read processing of the leak data dleak It is also possible to configure such that only the leak data dleak is not read out.

  With this configuration, it is not necessary to perform the reading process of the image data d and the reading process of the 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. In the case of the radiographic imaging apparatus 1 with a built-in battery as in the embodiment, it is possible to suppress wasteful consumption of the power of the battery 24 (see FIG. 7).

  For this reason, in the radiographic imaging device 1 with a built-in battery, as described above, after the reading process of the image data D as the main image and before the reading process of the offset data O, the reading process of the image data d and the reading of the leak data dleak are performed. It is considered that there are many cases where it is configured not to perform processing.

[About data transmission and preview image display in the present invention]
In the radiographic imaging system 50 and the radiographic imaging apparatus 1 configured as described above, for example, when a plurality of series of imaging (for example, imaging of the chest, abdomen, etc.) is performed on a single patient, Various processes have been performed as shown in FIG. In FIG. 36, FPD1 represents the radiation image capturing apparatus 1.

  That is, in the radiographic imaging device 1, first, reset processing of each radiation detection element 7 is performed. In the cooperation method, as described above, when a radiation engineer or the like operates the exposure switch 56 (see FIG. 13) of the radiation generator 58 and an irradiation start signal is transmitted from the radiation generator 58, the radiation The image capturing apparatus 1 transmits an interlock release signal when the reset process for one surface at that time is completed. Then, radiation is emitted from the radiation source 52 of the radiation generator 55.

  In the non-cooperation method, the detection process of the start of radiation irradiation is performed by the detection method 1 and the detection method 2 as described above. As described above, in the detection process, in the detection method 1, the readout process of the image data d is performed instead of the reset process of each radiation detection element 7, and in the detection method 2, the readout process of the leak data dleak and each radiation are performed. The reset process of the detection element 7 is alternately performed.

  When radiation irradiation to the radiographic imaging device 1 is started, the radiographic imaging device 1 applies an off-voltage to each of the lines L1 to Lx of the scanning line 5 and shifts to a charge accumulation state. When the irradiation is completed, a reading process of the image data D as the main image is performed. The read image data D is stored in the storage means 23 (see FIG. 7 and the like).

  When the radiation image capturing apparatus 1 finishes the reading process of the image data D, the radiation image capturing apparatus 1 uses the thinned data Dt (see FIGS. 11 and 12A and 12B) obtained by thinning out the data from the image data D at a predetermined rate. Send to console 58.

  On the console 58, as shown in FIG. 19, the preview image p_pre is displayed on the screen H2 of the display unit 58a based on the thinned data Dt transmitted. Then, a radiologist or the like looks at the preview image p_pre and determines whether or not re-imaging is necessary.

  In the radiographic imaging device 1, after the thinning data Dt is transmitted, the reset processing of each radiation detection element 7 is performed as many times as necessary as described above, and as described above, as shown in FIGS. The same processing sequence as the series of processing from before radiographic imaging to image data D reading processing is repeated, and offset data O acquisition processing including offset data O reading processing is performed.

  Then, the image data D and the offset data O are transmitted from the radiation image capturing apparatus 1, and the console 58 performs strict image processing on the image data D based on the image data D and the offset data O, and finally A typical radiation image p (see FIG. 20) is generated.

  In this case, as is well known in the field of electronic equipment, during the transmission of the image data D and the offset data O, the reset processing of each radiation detection element 7 and the read processing of the image data d and leak data dleak If this is done, various inconveniences such as abnormal values may be generated in the transmitted data, the read image data d, and the leak data dleak. For this reason, it is practically impossible to simultaneously perform data transmission, reset processing, and read processing.

  Therefore, after the transmission of all the image data D and offset data O is completed, the reset processing of each radiation detection element 7 for the next imaging and the detection processing by reading out the image data d and the leak data dleak are not performed until the next imaging. Is started.

  As described above, in the conventional series of shooting methods shown in FIG. 36, the process for the next shooting cannot be started unless the transmission of the image data D and the offset data O is completed. The cycle time Tcycle from the time when a radiation engineer or the like operates the exposure switch 56 to irradiate the radiation and the time when the radiation is irradiated in the next imaging is long.

  For this reason, as described above, the radiographic imaging system is not easy to use for radiographers and the like, and the patient has a long waiting time during imaging and feels inconvenient.

  Note that unless the radiographic engineer or the like determines the final radiographic image p (see FIG. 20) generated by the console 58 based on the image data D and offset data O transmitted from the radiographic imaging device 1 by the radiographic imaging system. There is a case where it is configured so that the next shooting cannot be performed. In such a case, the cycle time Tcycle from the previous shooting to the next shooting becomes further longer.

  Therefore, in order to solve this problem, the radiographic imaging system 50 according to the present embodiment is configured as follows. Hereinafter, processing in the radiographic image capturing apparatus 1 and the console 58 of the radiographic image capturing system 50 according to the present embodiment will be described, and the operation of the radiographic image capturing system 50 and the radiographic image capturing apparatus 1 according to the present embodiment will also be described. .

  In the present embodiment, as shown in FIG. 37, the radiographic image capturing apparatus 1 transmits thinned data Dt extracted from the image data D read from each radiation detecting element 7 to the console 58 every time imaging is completed. The console 58 repeats the process of displaying the preview image p_pre based on the thinned data Dt on the display unit 58a. However, the radiographic image capturing apparatus 1 immediately detects the radiation for the next radiographing immediately after the offset data O acquisition process. The device 7 is configured to shift to reset processing of the element 7 and detection processing of radiation irradiation start.

  At that time, the read image data D and offset data O are kept stored in the storage unit 23 of the radiation image capturing apparatus 1. When a series of imaging is completed, the image data D and offset data O obtained by each radiographic imaging are transmitted to the console 58 for the first time.

  That is, in this embodiment, only the thinning data Dt is transmitted from the radiographic imaging apparatus 1 to the console 58 for each radiographing, and the image data D and the offset data O are the first when a series of radiographing is completed. Sent to console 58.

  In addition, when a radiographer or the like who has seen the preview image p_pre determines that imaging is not performed well and re-imaging is necessary and clicks the “NG” button (see FIG. 19), as described above. In addition, the console 58 cancels the association of the thinning data Dt with the imaging order information to delete the thinning data Dt, and transmits a deletion signal to the radiographic image capturing apparatus 1.

  Then, the radiographic image capturing apparatus 1 that has received the erasure signal erases the image data D read from each radiation detection element 7 during the radiographing from the storage means 23 and performs the offset data O acquisition process. In this case, the acquisition process is stopped, and if the offset data O is acquired by the offset data O acquisition process, the acquired offset data O is deleted from the storage unit 23.

  As described above, as shown in FIG. 37, only the thinning data Dt is transmitted for each photographing, and the image data D and the offset data O obtained by each photographing are transmitted after a series of photographing. It becomes possible to shorten the cycle time Tcycle from the time when the radiation technician or the like operates the exposure switch 56 to irradiate the radiation in the previous imaging until the next imaging irradiates the radiation.

  Therefore, even when imaging is performed continuously, it is possible to perform imaging continuously with a short cycle time Tcycle, and the radiographic imaging system 50 is easy to use for radiologists and the like, and the patient can perform imaging. Therefore, the radiation image capturing system 50 is convenient for the patient.

  In the present embodiment, as described above, the data transmitted from the radiation image capturing apparatus 1 to the console 58 for displaying the preview image p_pre is thinned data Dt having a data amount smaller than that of the image data D. Therefore, the time required for transmitting the thinned data Dt is shorter than the time required for transmitting all the image data D.

  Therefore, it is possible to shorten the transmission time of the data transmitted for each photographing (that is, the thinned data Dt) as much as possible, and also in this respect, the cycle time Tcycle can be further shortened.

[Modification]
In order to further shorten the cycle time Tcycle for each photographing, for example, as in the present embodiment shown in FIG. 37, the offset data O acquisition processing including the offset data O reading processing is performed for each photographing. Instead, the offset data O acquisition process can be performed after a series of radiographic image capturing is completed.

  That is, although illustration is omitted, after the image data D is read out in a certain shooting and the thinned data Dt is transmitted, the offset data including the processes of reset → charge accumulation → O read in FIG. Without performing the O acquisition process, it is possible to immediately shift to the reset process of each radiation detection element 7 or the detection process of the start of radiation irradiation for the next imaging.

  If comprised in this way, the cycle time Tcycle after a radiation engineer etc. will operate the exposure switch 56 at the time of previous imaging | photography, and will irradiate with radiation by the next imaging | photography can further be shortened. This makes it possible for the radiographic imaging system 50 to be more convenient for radiologists and the like, and further reduces the time that the patient waits during imaging, making the radiographic imaging system 50 even more convenient for the patient. Become.

  As described above, in the non-cooperative method, in the detection method 1 and the detection method 2 for detecting the start of radiation irradiation, in order to increase the detection sensitivity, the on time T for turning on the TFT 8 in the reading process of the image data d is set. The transmission interval τ of the pulse signals Sp1 and Sp2 in the reading process of the leak data dleak is increased (in the case of the detection method 2, see FIG. 34). There is a case.

  Therefore, in the case of the detection method 1, the time required for the reading process for one surface of the detection unit P performed by sequentially applying the ON voltage to each of the lines L1 to Lx of the scanning line 5 in the reading process of the image data d is long. Thus, in the case of the detection method 2, the on-voltage is sequentially applied to the lines L1 to Lx of the scanning line 5 in the reset process of the radiation detection elements 7 performed together with the reading process of the leak data dleak. The time required for the reset process becomes longer.

  In this case, as described above, the acquisition process of the offset data O is performed by repeating the same processing sequence as the series of processes from the detection process before radiographic image capturing to the readout process of the image data D through the charge accumulation state. With this configuration, the time required for the detection process before the read process of the offset data O (described as “O read” in FIG. 37) increases.

  As described above, particularly in the non-cooperation method, when the ON time T and the transmission interval τ are increased, the time until the offset data O is acquired increases, and as a result, the cycle time Tcycle tends to increase. However, as described above, the configuration in which the acquisition process of the offset data O is performed after a series of imaging is completed, and the cycle time Tcycle is further shortened, so that the radiographic imaging system 50 is more convenient for a radiographer or the like. It is possible to more effectively exhibit the above-mentioned beneficial effects such as a better quality.

  On the other hand, in the present embodiment, as described above, after a series of radiographic image capturing is completed, the image data D is transmitted together with the offset data O. At this time, among the image data D for each imaging, thinned data is transmitted. Dt has already been transmitted to the console 58 for each shooting.

  Therefore, when a series of radiographic image capturing is completed, the remaining image data D other than the thinned data Dt among the image data D obtained by the radiographic image capturing from the radiographic image capturing apparatus 1 is transmitted to the console 58. In 58, the original image data D for each photographing can be restored by combining the thinned data Dt that has already been transmitted and the remaining image data D that has been transmitted.

  If comprised in this way, it will become possible to shorten the transmission time of image data D etc. after a series of imaging | photography is complete | finished. Therefore, especially in the radiographic imaging apparatus 1 incorporating the battery 24 (see FIG. 7) as in the present embodiment, there is an advantage that the power consumption of the battery 24 can be further reduced.

  As described above, according to the radiographic image capturing system 50 and the radiographic image capturing apparatus 1 according to the present embodiment, a series of cases both in the case of shooting with the cooperative method and the case of shooting with the non-cooperative method. During the radiographic imaging, only the thinning data Dt is transmitted from the radiographic imaging device 1 to the console 58, and after the series of radiographic imaging is completed, each image data obtained in each radiographic imaging is obtained. D and offset data O are transmitted to the console 58.

  For this reason, since the thinned data Dt is transmitted for each shooting, the amount of data to be transmitted is reduced and the transmission time is shortened. Therefore, the preview image p_pre is displayed quickly and accurately on the display unit 58a of the console 58. Is possible. Therefore, a radiographer or the like can quickly and accurately determine whether or not re-imaging is necessary.

  In addition, since image data D and offset data O are not transmitted during a series of imaging, it does not take time to transmit image data D and offset data O. It becomes possible to shorten the cycle time Tcycle from the time when the exposure switch 56 is operated to irradiate the radiation to the time when the next imaging is irradiated with the radiation.

  Therefore, the radiographer or the like can immediately prepare for the next radiographing after the radiographing is completed, and the radiographic image capturing system 50 can be made easy to use for the radiographer or the like. In addition, the time that the patient waits during imaging is shortened, and the radiographic imaging system 50 can be made convenient for the patient.

  In the above-described embodiment, for example, it is possible for a radiologist or the like to set the number of radiographic image captures to be performed in advance (that is, the number of radiation irradiations) on the console 58 in advance. . In this case, when information such as the number of imaging is transmitted from the console 58 to the radiographic image capturing apparatus 1, the control means 22 of the radiographic image capturing apparatus 1 stores it and the radiographic image capturing is performed a set number of times. The image data D and the offset data O can be immediately transmitted to the console 58.

  When a series of radiographing is completed, a radiographer or the like operates the console 58 and makes a transmission request to the radiographic imaging device 1. It is also possible to configure to transmit data O.

  Further, in the above-described embodiment, in the case of the non-cooperative method, the image data d and the leak data dleak are read before radiographic imaging, and radiation irradiation is performed based on the read image data d and the leak data dleak. A case has been described in which the start is detected or the leakage data dleak is read in the charge accumulation state, and the end of radiation irradiation is detected based on the read leakage data dleak.

  However, instead of the configuration as described above, as described above, when the radiation image capturing apparatus 1 is irradiated with radiation, the amount of current flowing through the wiring in the radiation image capturing apparatus 1 may increase. It is also possible to use such a configuration that current detection means is provided to detect the start and end of radiation irradiation.

  For example, when the radiation imaging apparatus 1 is irradiated with radiation, an electric charge is generated in each radiation detection element 7, so that the second electrode 7 b (see FIG. 7 etc.) of the radiation detection element 7 to which a bias voltage is applied. The potential of the first electrode 7a changes. Therefore, the amount of current flowing through the bias line 9 connected to the second electrode 7b and the connection 10 increases.

  As described above, when the radiation image capturing apparatus 1 is irradiated with radiation, the bias line 9, the connection line 10, the scanning line 5, the power supply circuit 15 a of the scanning drive unit 15 and the gate driver provided in the radiation image capturing apparatus 1. The value of the current flowing in each wiring such as the wiring 15d (see FIG. 7) connecting to 15b increases.

  Therefore, the current detection means 26 is provided at a position where the connection 10 of the bias line 9 is connected to the bias power supply 14, for example, as shown in FIG. The current value output from the current detection means 26 is monitored. Then, for example, by setting a threshold value for the current value, it is possible to determine that radiation irradiation has started when the current value exceeds the threshold value.

  Further, when radiation irradiation to the radiographic image capturing apparatus 1 is completed, the value of the current flowing through the wirings is reduced to the original value. In view of this, it is possible to use the decrease in current to determine that the irradiation of radiation has been completed when the value of the current decreases below a threshold value.

  Even in the case where it is configured to detect the start of irradiation of radiation to the radiographic imaging apparatus 1 based on the current value detected by the current detection means 26 provided in the apparatus in this way, for each imaging. It is possible to apply the present invention by transmitting the thinning data Dt from the radiographic image capturing apparatus 1 to the console 58 and transmitting the image data D and the offset data O after the end of a series of imaging.

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 D Image Data Dt Thinning Data O Offset Data P Detection Unit p Radiation Image p_pre Preview Image q Charge r Region

Claims (6)

In a radiographic imaging system comprising: a radiographic imaging device that acquires image data by radiographic imaging; and a console that includes a display unit that displays a radiographic image.
The radiographic image capturing apparatus includes:
A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; A detector comprising:
Scanning drive means for sequentially applying an on-voltage to each of the scanning lines while switching the scanning lines to which an on-voltage is applied;
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;
Control means for controlling at least the scanning drive means and the readout circuit to perform readout processing of the image data from the radiation detection element;
A communication means for transmitting and receiving signals to and from the console;
With
In a predetermined series of radiographic image capturing, the control means of the radiographic image capturing apparatus reads the image data from the image data read from the radiation detecting elements at a predetermined time each time radiographic image capturing is completed. Thinning out data at a rate to create thinned data and sending it to the console. When the thinned data is transmitted from the radiographic imaging device, the console displays a preview image based on the thinned data on the display unit. Repeat
The control means of the radiographic imaging device transmits the image data obtained by radiographic imaging to the console when the predetermined series of radiographic imaging is completed. Shooting system. The control means of the radiographic image capturing device, when the predetermined series of radiographic image capturing is completed, out of the image data obtained by the radiographic image capturing, the remaining image data other than the thinned data Send to the console,
The radiographic imaging system according to claim 1, wherein the console restores the original image data by combining the thinned data that has already been transmitted and the remaining image data that has been transmitted. . The control means of the radiographic image capturing apparatus includes:
In a predetermined series of radiographic image capturing, after each radiographic image capturing is completed, after transmission of the thinned data to the console, offset data corresponding to an offset due to dark charge superimposed in the image data is obtained. Perform the acquisition process of the offset data to be acquired,
3. The offset data is transmitted to the console together with the image data obtained in each radiographic image capture when the predetermined series of radiographic image captures is completed. Radiation imaging system.   The control means of the radiographic image capturing apparatus acquires offset data corresponding to an offset due to dark charges superimposed on the image data when the predetermined series of radiographic image capturing is completed. The radiographic image capturing system according to claim 1, wherein a data acquisition process is performed, and the offset data is transmitted to the console together with the image data obtained by radiographic image capturing.   The acquisition processing of the offset data in the radiographic imaging device is performed by repeating the same processing sequence as a series of processing from processing before imaging in radiographic imaging to readout processing of the image data. The radiographic imaging system of Claim 3 or Claim 4. A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; A detector comprising:
Scanning drive means for sequentially applying an on-voltage to each of the scanning lines while switching the scanning lines to which an on-voltage is applied;
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;
Control means for controlling at least the scanning drive means and the readout circuit to perform readout processing of the image data from the radiation detection element;
A communication means for transmitting and receiving signals to and from the console;
With
The control means includes
In each of a predetermined series of radiographic image capturing, every time radiographic image capturing is completed, the image data is thinned out at a predetermined rate from the image data read from each of the radiation detection elements, and thinned data is created. To the console,
The control means of the radiographic imaging device transmits the image data obtained by radiographic imaging to the console when the predetermined series of radiographic imaging is completed. Shooting device.

Images