JP2013000372A - Radiographic imaging system and radiographic imaging apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiographic imaging system that photographs a moving subject or the like in a radiographic imaging apparatus as a quasi-moving image and is able to reproduce the quasi-moving image photographed by the radiographic imaging apparatus.SOLUTION: The radiographic imaging system 50 includes: the radiographic imaging apparatus 1; a radiation generator 55 with a radiation source 52; and a console 58 for generating a radiograph based on image data. When radiographs are photographed in series, control means for the radiographic imaging apparatus 1 measures a time interval for each radiographing. Also, when image data obtained by photographing the radiographs in series is transmitted to the console 58, this control means transmits information about each time interval so that it is correlated with corresponding image data. The console 58 correlates the information about each time interval with each formed radiograph.

Description

  The present invention relates to a radiographic image capturing system and a radiographic image capturing device, and more particularly to a radiographic image capturing system that captures a so-called quasi-moving image by the radiographic image capturing device and a radiographic image capturing device used therefor.

  A so-called direct-type radiographic imaging device that generates electric charges by a detection element in accordance with the dose of irradiated radiation such as X-rays and converts it into an electrical signal, or other radiation such as visible light with a scintillator Various types of so-called indirect radiographic imaging devices have been developed that convert charges into electromagnetic signals after they have been converted into electromagnetic waves of a wavelength, and then generated by photoelectric conversion elements such as photodiodes in accordance with the energy of the converted and irradiated electromagnetic waves. Yes. In the present invention, the detection element in the direct type radiographic imaging apparatus and the photoelectric conversion element in the indirect type radiographic imaging apparatus are collectively referred to as a radiation detection element.

  This type of radiographic imaging apparatus is known as an FPD (Flat Panel Detector), and has been conventionally formed integrally with a support base (see, for example, Patent Document 1). A portable radiographic image capturing apparatus housed in the box has been developed and put into practical use (see, for example, Patent Documents 2 and 3).

  By the way, such a radiographic image capturing apparatus is generally configured to capture a radiographic image as a still image, and is not configured to capture a moving image. However, when radiographic images for medical diagnosis are taken using such a radiographic imaging device, for example, a respiratory organ such as a lung that expands or contracts due to breathing, a blood flow including a heartbeat, etc. There is also a request from the medical field that they want to shoot moving organs in a moving image. There is also a desire to perform imaging by continuously irradiating a subject multiple times from multiple directions like tomosynthesis imaging.

  Therefore, in Patent Document 4, for example, a configuration in which an additional function module can be detachably connected in a casing of a portable radiographic imaging device, and when the additional function module is connected, the radiographic imaging device is in a stationary imaging mode. An invention of a portable radiographic image capturing apparatus is disclosed in which, when image capturing is switched to moving image capturing and the additional function module is removed, the image capturing mode is switched from moving image capturing to still image capturing.

  And, in the radiation image capturing apparatus in a state where the additional function module is not connected, it is difficult to capture a moving image, but by providing various functional units necessary for moving image capturing in the connected additional function module, Such a radiation image capturing apparatus can also perform moving image capturing.

JP-A-9-73144 JP 2006-058124 A JP-A-6-342099 JP 2008-83031 A

  By the way, in a medical site, there is a case where a portable radiographic image capturing device is used by being loaded into an existing Bucky device 51 in the photographing room R1 (see FIG. 11 described later). However, the existing Bucky device 51 is a conventional one. Many are configured to load a CR (Computed Radiography) cassette. The CR cassette is formed so as to have a thickness of at least 15 mm + 1 mm to 15 mm-2 mm in accordance with the JIS standard size (corresponding international standard is IEC 60406) for conventional screen film cassettes. It was.

  For this reason, the portable radiographic image capturing apparatus may be required to be formed with dimensions conforming to the JIS standard size as in the case of such a CR cassette. However, it is not always easy to configure the additional function module so that it can be accommodated in the housing of the radiographic imaging apparatus as described above under such size restrictions.

  On the other hand, not limited to the portable radiographic imaging apparatus as described above, generally, radiographic imaging apparatus shoots blood flow including respiratory expansion / contraction and heart beat in a moving image or tomosynthesis imaging. In such a case, it is not always necessary to shoot them at 30 frames per second like a normal movie so that the movement can be seen continuously with the naked eye. In many cases, it may be taken as a so-called quasi-moving picture that is taken intermittently in time series at a rate of one frame per frame or several seconds.

  In this case, when a doctor or the like reproduces and displays a plurality of images such as an inflating / deflating respiratory image taken as a quasi-moving image, a plurality of still images constituting the quasi-moving image may be reproduced one by one. However, a plurality of still images may be reproduced and displayed at an actual time interval at the time of shooting. For this reason, it is necessary to accurately transmit information on each time interval between each photographing when each still image is photographed to an image display device that reproduces and displays a semi-moving image.

  In this case, the radiation source 52 (see FIGS. 11 and 12 to be described later) is configured to obtain from the radiation generator 55 the timing at which the radiation image capturing apparatus is irradiated with radiation through the subject, that is, the information on the time interval. Although it is possible, the radiation generator 55 existing in the facility is often not configured to measure the time interval from the last irradiation with radiation.

  In such a case, if the radiation generator 55 is modified to measure the above time interval, there may be a problem such as cost. Therefore, it is desirable that the time interval is measured not on the radiation generating device 55 but on the radiation image capturing device side.

  The present invention has been made in view of the above points, and a moving subject or the like was photographed as a quasi-moving image by the radiographic image capturing device, and a plurality of still images constituting the quasi-moving image were captured by the radiographic image capturing device. It is an object of the present invention to provide a radiographic imaging apparatus capable of measuring a time interval for each imaging, and a radiographic imaging system capable of reproducing a series of still images as a quasi-movie based on the measured time intervals. To do.

  At that time, a control configuration in a conventional radiographic imaging apparatus that captures only a still image, and data when image data D and the like are transmitted from the radiographic imaging apparatus to a console 58 (see FIGS. 11 and 12 described later). If the time interval information can be transmitted without making a major change to the configuration or the like, the above object can be achieved without making a major change to the processing in the radiographic imaging apparatus or the console 58. This is desirable.

  Thus, as described above, the present invention provides a console with the control configuration, image data, and the like in a conventional radiographic imaging apparatus that captures only a still image when a moving subject is captured as a semi-moving image by the radiographic imaging apparatus. It is another object of the present invention to provide a radiographic image capturing apparatus and a radiographic image capturing system that can achieve the above object without greatly changing the data configuration at the time of transmission.

In order to solve the above problems, the radiographic image capturing system and radiographic image capturing apparatus of the present invention include:
A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other, and a plurality of radiation detection elements arranged in a two-dimensional manner in each small region partitioned by the plurality of scanning lines and the plurality of signal lines A detection unit comprising:
Scan driving means for applying an on voltage or an off voltage to each of the scanning lines;
Switch means connected to each of the scanning lines and causing the signal lines to discharge charges accumulated in the radiation detection element when an on-voltage is applied;
A readout circuit that converts the electric charge emitted from the radiation detection element into image data and reads the image data;
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 capable of communicating with an external device;
A radiographic imaging device comprising:
A radiation generator comprising a radiation source for irradiating the radiation imaging apparatus with radiation;
A console that generates a radiographic image based on the image data transmitted from the radiographic imaging device;
With
The control means of the radiographic imaging device measures a time interval for each radiographic imaging when a series of radiographic imaging is performed, and obtained by the series of radiographic imaging When transmitting each image data to the console, the information of each time interval is associated with each corresponding image data and transmitted to the console,
The console associates each time interval information associated with each image data with each radiation image generated based on the image data transmitted from the radiation image capturing apparatus. To do.

  According to the radiation image capturing system and the radiation image capturing apparatus of the system as in the present invention, the control means can be used without providing an additional function module for capturing a moving image as in the conventional radiation image capturing apparatus. By simply measuring the time interval for each radiographic image capture in a series of radiographic images, information on the display time interval when displaying each radiographic image obtained by a series of radiographs, that is, each still image in a quasi-moving manner, is obtained. It becomes possible to acquire accurately.

  Therefore, it is possible to accurately capture a moving subject or the like as a quasi-moving image using a conventional radiographic image capturing apparatus that captures only a still image. In addition, it is not necessary to modify the radiation generating apparatus so as to measure the time interval, and the time interval can be measured on the radiation image capturing apparatus side.

  Also, in order to associate time interval information with each radiographic image, that is, each still image, generated based on the image data obtained by each radiographic image capture, etc., in the console, each still image obtained by a series of image captures An image display device that reproduces in a semi-moving manner reproduces each still image in accordance with a time interval associated with each still image, thereby expanding the movement of an organ such as a lung that expands or contracts to a radiographic image capturing device. Can be played back at the time interval taken. Therefore, each still image obtained by a series of radiographic image capturing can be accurately displayed in a quasi-moving manner.

It is a perspective view which shows the external appearance of the radiographic imaging apparatus which concerns on this embodiment. It is sectional drawing which follows the XX line in FIG. It is a perspective view which shows the external appearance of the radiographic imaging apparatus of the state which connected the cable. It is a top view which shows the structure of the board | substrate of a radiographic imaging apparatus. It is an enlarged view which shows the structure of the radiation detection element, TFT, etc. which were formed in the small area | region on the board | substrate of FIG. It is a side view explaining the board | substrate with which a flexible circuit board, a PCB board | substrate, etc. were attached. It is a block diagram showing the equivalent circuit of a radiographic imaging apparatus. It is a block diagram showing the equivalent circuit about 1 pixel which comprises a detection part. It is a timing chart showing the ON / OFF timing of the charge reset switch and TFT in the reset processing of each radiation detection element. 6 is a timing chart showing charge reset switches, pulse signals, and TFT on / off timings in image data read processing. It is a figure which shows the structural example of the radiographic imaging system which concerns on this embodiment constructed | assembled in the imaging | photography room. It is a figure which shows the structural example of the radiographic imaging system which concerns on this embodiment constructed | assembled on the round-trip vehicle. It is a 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 read processing is repeatedly performed before radiographic image capturing in the non-cooperative detection method 1; 6 is a timing chart illustrating an example of timing for sequentially applying an on-voltage to each scanning line when configured to stop the image data reading process at the time when the start of radiation irradiation is detected in the case of the detection method 1; 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. Timing chart for explaining the timing of applying an ON voltage to each scanning line when leak data reading processing and reset processing are alternately performed before radiographic imaging in detection method 2 and leak data reading processing is performed in a charge accumulation state It is. It is a figure explaining the procedure of the process performed with a radiographic imaging apparatus in a series of radiographic imaging, and the time interval for every imaging. It is a figure showing the image data read from each radiation detection element. It is a figure showing the example of the thinning data extracted from image data. It is a figure explaining writing of the information of a time interval to the predetermined | prescribed pixel part of each image data obtained by each radiographic imaging. It is a histogram showing the example of distribution of the appearance frequency of image data. It is a histogram showing the example of distribution of the appearance frequency of the image data at the time of imaging | photography the imaging | photography site | part different from FIG. It is a histogram showing the example of distribution of normal distribution assumed about distribution of appearance frequency of image data. It is a histogram which shows distribution of the appearance frequency of each difference of the image data of the radiation detection element adjacent to a signal line direction. It is a figure showing the data for preview images put together virtually. It is a figure explaining the difference of the image data D obtained by each imaging | photography about the same radiation detection element being calculated. 6 is a timing chart for explaining that offset data reading processing is performed by repeating a series of processing sequences up to image data reading processing.

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

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

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

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

  In the present embodiment, a hollow rectangular tube-shaped housing body 2A having a radiation incident surface R in the housing 2 is formed of a material such as a carbon plate or plastic that transmits radiation, and the housing body 2A. The housing 2 is formed by closing the opening portions on both sides with lid members 2B and 2C.

  Further, the lid member 2B on one side of the housing 2 has a power switch 37, a changeover switch 38, a connector 39, an indicator 40 composed of an LED or the like for displaying a battery state, an operating state of the radiographic imaging apparatus 1, and the like. Is arranged.

  As shown in FIG. 3, in this embodiment, the connector 39 can be connected to a connector C provided at the tip of the cable Ca. Then, by being connected to the cable Ca, for example, signals and the like can be transmitted to and received from a console 58 (see FIG. 11 and FIG. 12) described later, and image data D and the like can be transmitted to the console 58. It has become.

  Although not shown, for example, the antenna device 41 (see FIG. 7 described later) is provided in the lid member 2C on the opposite side of the housing 2, for example, by being embedded in the lid member 2C. Thus, in the present embodiment, the connector 39 and the antenna device 41 are used as communication means for transmitting and receiving signals between the radiographic imaging device 1 and the console 58 and transmitting image data D and the like to the console 58. It is supposed to function.

  As shown in FIG. 2, a substrate 4 is disposed inside the housing 2 via a lead thin plate (not shown) on the upper surface side of the base 31, and an electronic component is disposed on the lower surface side of the base 31. A PCB substrate 33, a battery 24, and the like on which 32 and the like are disposed are attached. Further, a glass substrate 34 for protecting the substrate 4 and the radiation incident surface R of the scintillator 3 is disposed. Moreover, in this embodiment, the buffer material 35 for preventing that they collide between the base 31, the board | substrate 4, etc., 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, that is, an electromagnetic wave centered on visible light and output when receiving radiation. .

  In the present embodiment, the substrate 4 is made 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.

  In this way, the entire small region r provided with a plurality of radiation detection elements 7 arranged two-dimensionally 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 area to be detected is the 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 radiographic imaging apparatus 1 and is irradiated with electromagnetic waves such as visible light converted from the radiation by the scintillator 3, the radiation detection element 7 has electron positive inside. Generate hole pairs. In this way, the radiation detecting element 7 converts the irradiated radiation (electromagnetic wave converted from the radiation by the scintillator 3 in this embodiment) into electric charge.

  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 (Chip On Film or the like) on which a chip such as a gate IC 15c constituting a gate driver 15b of a scanning driving means 15 described later is incorporated on a film. 12) are connected via an anisotropic conductive adhesive material 13 such as an anisotropic conductive adhesive film (Anisotropic Conductive Film) or an anisotropic conductive paste (Anisotropic Conductive Paste).

  The flexible circuit board 12 is routed to the back surface 4b side of the substrate 4 and connected to the PCB substrate 33 described above on the back surface 4b side. 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 includes a power supply circuit 15a for supplying an on voltage and an off voltage to the gate driver 15b via the wiring 15d, and a voltage applied to each line L1 to Lx of the scanning line 5 between the on voltage and the off voltage. A gate driver 15b that switches between the on state and the off state of each TFT 8 is provided.

  As shown in FIGS. 7 and 8, each signal line 6 is connected to each readout circuit 17 built in the readout IC 16. The readout circuit 17 includes an amplification circuit 18 and a correlated double sampling circuit 19. An analog multiplexer 21 and an A / D converter 20 are further provided in the read IC 16. 7 and 8, the correlated double sampling circuit 19 is represented as CDS. In FIG. 8, the analog multiplexer 21 is omitted.

In the present embodiment, the amplifier circuit 18 is a charge amplifier circuit including an operational amplifier 18a, a capacitor 18b and a charge reset switch 18c connected in parallel to the operational amplifier 18a, and a power supply unit 18d that supplies power to the operational amplifier 18a and the like. It consists of 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. Each TFT 8 is turned on in the state (and the switch 18e is turned off).

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

  On the other hand, at the time of read processing of image data D from each radiation detection element 7 or read processing of image data d for irradiation start detection to be described later, as shown in FIG. When charges are released from the radiation detection elements 7 to the signal lines 6 through the TFTs 8 that are turned on in a state where the switch 18e is turned off (and the switch 18e is turned on), the charges are amplified. Is stored in the condenser 18b.

  In the amplifier circuit 18, a voltage value corresponding to the amount of charge accumulated in the capacitor 18b is output from the output side of the operational amplifier 18a. The correlated double sampling circuit (CDS) 19 outputs the pulse signal Sp1 (see FIG. 10) from the control means 22 before the electric charge flows out from each radiation detection element 7, and at that time, the correlation double sampling circuit (CDS) 19 outputs it from the amplifier circuit 18. Holds the voltage value Vin.

  Then, after the electric charge flowing out from each radiation detection element 7 is accumulated in the capacitor 18b of the amplifier circuit 18, when the pulse signal Sp2 is transmitted from the control means 22, the voltage value output from the amplifier circuit 18 at that time point. Holds Vfi. Then, a voltage value difference Vfi−Vin is calculated, and the calculated difference Vfi−Vin is output downstream as analog value image data D.

  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 the digital value is sequentially converted by the A / D converter 20. It is converted into image data D, outputted 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, etc., not shown, connected to a bus, an FPGA (Field Programmable Gate Array), or the like. It is configured. It may be configured by a dedicated control circuit.

  And the control means 22 controls operation | movement etc. of each member of the radiographic imaging apparatus 1. Further, as shown in FIG. 7 and the like, the control means 22 is connected to a storage means 23 composed of SRAM (Static RAM), SDRAM (Synchronous DRAM) or the like.

  In the present embodiment, the antenna unit 41 described above is connected to the control unit 22, and each member such as the detection unit P, the scanning drive unit 15, the readout circuit 17, the storage unit 23, the bias power source 14, etc. A battery 24 for supplying electric power is connected. The battery 24 is connected to the connector 39 described above, and power is supplied from a charging device (not shown) via the connector 39 when the battery 24 is charged.

  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.

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

  In the photographing room R1, a bucky device 51 is installed, and the bucky device 51 can be used by loading the radiographic imaging device 1 in its cassette holding part (also referred to as a cassette holder) 51a. It has become. FIG. 11 shows a case where a bucky device 51A for standing position shooting and a bucky device 51B for standing position shooting are installed as the bucky device 51. For example, a bucky device for standing position 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. 3, the radiographic image capturing apparatus 1 is connected to the bucky device 51 in a state where the connector 39 of the radiographic image capturing apparatus 1 and the connector C provided at the tip of the cable Ca are connected. Can be loaded. A connector C may be provided in the cassette holding portion 51a of the bucky device 51 so that the connector 39 and the connector C are automatically connected when the radiographic image capturing device 1 is loaded. Yes, as appropriate.

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

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

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

  In the present embodiment, the front room (also referred to as 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.

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

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

  As shown in FIG. 11, in the present embodiment, a console 58 formed of a computer or the like is provided in the front chamber R2. The console 58 can be configured to be provided outside the imaging room R1 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, as will be described later, when the thinning data Dt is transmitted from the radiation image capturing apparatus 1, the console 58 displays a preview image p_pre on the display unit 58a based on the data.

  As will be described later, the console 58 generates a radiation image p based on the image data D or the like when the image data D or the like is transmitted from the radiation image capturing apparatus 1.

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

  When the radiographic imaging apparatus 1 is used in this way, for example, as shown in FIG. 3, if the cable C is connected to the connector 39 of the radiographic imaging apparatus 1, the cable C interferes with the work of the radiographer. In this embodiment, when the radiographic imaging device 1 is used alone, the connector 39 is used without being connected to the cable C.

  Further, when the radiographic imaging apparatus 1 is used in the hospital room R3 or the like, the radiation generator 55 or the radiation source 52A installed in the imaging room R1 cannot be brought into the hospital room R3. Therefore, as shown in FIG. 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.

  In addition, as shown in FIG. 11, the radiographic imaging device 1 is inserted between the patient's body lying on the bucky device 51B for supine photography in the photographing room R1 and the bucky device 51B for supine photography. It can also be used by being applied to the patient's body on the bucky device 51B for lying position photography. It is also possible to use it.

  Further, in the case of the radiographic imaging system 50 constructed on the round wheel 71 shown in FIG. 12, the console 58 performs a display process of the preview image p_pre on the display unit 58a described later to obtain a final radiographic image. The generation of p or the like may be performed by another console 58 having a generation processing function.

[Processing up to read-out processing of image data D in the radiation imaging apparatus]
Here, in the radiographic image capturing system 50, radiation is applied to the radiographic image capturing device 1, and the radiographic image capturing device 1 and the radiation generating device 50, etc., until the image data D is read from each radiation detection element 7, respectively. Processing will be described.

  As shown in FIG. 11, when the radiographic imaging system 50 is constructed in the imaging room R <b> 1 or the like, the radiographic imaging apparatus 1 and the radiation generation apparatus 55 transmit signals via the relay 54. It is possible to perform radiographic imaging while exchanging and coordinating with the radiographic imaging device 1 and the radiation generation device 55. Hereinafter, such a photographing method is referred to as a cooperative method.

  In addition, as shown in FIG. 12, the radiographic image capturing apparatus 1 and the radiation generating apparatus 55 cannot exchange signals as in the case where the radiographic image capturing system 50 is constructed on the round wheel 71. In such a case, it is necessary to detect that the radiation image capturing apparatus 1 itself has irradiated the radiation. Hereinafter, such a photographing method is referred to as a non-cooperative method.

  In the present embodiment, the radiographic image capturing apparatus 1 can perform radiographic image capturing using either a cooperative method or a non-cooperative method depending on the situation. The present invention can also be applied to a radiographic imaging apparatus that can perform radiographic imaging only by any one of the systems.

[Processing in linkage mode]
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, the process illustrated in FIG. 9 is performed for each of the lines L <b> 1 to Lx of the scanning line 5.

  Specifically, the control unit 22 of the radiographic image capturing apparatus 1 performs, for example, as shown in FIG. 13, from the gate driver 15 b (see FIG. 7) of the scanning driving unit 15 to each line L <b> 1 to Lx of the scanning line 5. The on-voltage is sequentially applied, the on-voltage is sequentially applied to the gate electrode 8g of each TFT 8 to turn on the TFT 8, and the charge remaining in each radiation detection element 7 is discharged to the signal line 6, respectively.

  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 wait for the start of radiation irradiation in a state where all the TFTs 8 are turned off.

  In addition, when waiting for the start of radiation irradiation with all the TFTs 8 in the OFF state in this way, the amount of dark charge accumulated in each radiation detection element 7 becomes longer as the time until the radiation irradiation starts becomes longer. It will increase. Therefore, from the viewpoint of performing imaging with less charge remaining on each radiation detection element 7 such as a dark charge, the reset processing of each radiation detection element 7 may be repeated until immediately before the start of radiation irradiation. Is possible.

  In this case, for example, as shown in FIG. 14, during the reset process Rm for one surface, the radiation switch 56 (see FIG. 11 and FIG. 12) is operated by the radiation generator 55 by the radiation engineer to generate radiation. When the irradiation start signal is transmitted from the apparatus 55 to the radiographic image capturing apparatus 1, the control means 22 of the radiographic image capturing apparatus 1 performs the reset process Rm for one surface performed when the irradiation start signal is transmitted. Is completed, the reset process of each radiation 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.

  At the same time, the controller 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 the cooperation method, radiation is emitted to the radiation image capturing apparatus 1 while exchanging an irradiation start signal, an interlock release signal, and the like between the radiation image capturing apparatus 1 and the radiation generating apparatus 55. Yes.

  Further, when the control unit 22 of the radiographic image capturing apparatus 1 transmits the interlock release signal as described above, the charge storage state is maintained for a predetermined time. Then, after a predetermined time has elapsed, as shown in FIG. 15, on-voltages are sequentially applied to the lines L <b> 1 to Lx of the scanning line 5, and the image data D is read from each radiation detection element 7. Yes. In addition, the diagonal line in FIG. 15 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.

[Processing in the case of non-linking method]
Next, processing when radiographic imaging is performed in a non-cooperative manner will be described. In this case, as described above, since signals are not exchanged between the radiographic image capturing apparatus 1 and the radiation generating apparatus 55, it is necessary to detect that radiation has been irradiated by the radiographic image capturing apparatus 1 itself. It becomes.

  In this case, it is also possible to provide a new sensor or means for detecting the start of radiation irradiation in the radiation image capturing apparatus 1. However, as described above, when considering the size limitation of the housing 2 in the radiographic image capturing apparatus 1 and the configuration of the radiographic image capturing apparatus 1 that captures only a conventional still image, etc., For example, the radiation image capturing apparatus 1 itself can be configured to detect the start of radiation irradiation using the respective function units already provided in the radiation image capturing apparatus 1 as follows.

  Hereinafter, two detection methods will be described as an example of a method for detecting radiation irradiation by the radiographic image capturing apparatus 1 itself using each function unit already provided in the radiographic image capturing apparatus 1.

[Detection method 1]
For example, as shown in FIG. 16, instead of performing reset processing (see FIG. 13 and the like) of each radiation detection element 7 before radiographic imaging as in the case of the above-described cooperation method, scanning before radiographic imaging is performed. It is possible to apply a turn-on voltage to the lines L1 to Lx of the scanning line 5 sequentially from the gate driver 15b of the driving unit 15 and to repeatedly read out the image data d from each radiation detection element 7. is there.

  In addition, the image data read in the reading process before radiographic image capturing is hereinafter referred to as image data d for irradiation start detection, in distinction from the image data D as the main image read immediately after imaging. The image data D as the main image is simply referred to as main image data D.

  Further, in the reading process of the image data d for detecting the start of irradiation, on / off of the charge reset switch 18c of the amplifier circuit 18 of the read circuit 17, transmission of the pulse signals Sp1, Sp2 to the correlated double sampling circuit 19, etc. The processing is the same as the processing in the reading processing of the main image data D shown in FIG.

  As described above, when the reading processing of the image data d for detecting the start of irradiation is performed before the radiographic image capturing, as shown in FIG. Image data d read at the time (in FIG. 17, image data d read by applying an on-voltage to the line Ln of the scanning line 5) was read before that, as shown in FIG. The value is much larger than the image data d (see time t1 in FIG. 18).

  Therefore, the control means 22 is configured to monitor the irradiation start detection image data d read in the reading process before radiographic image capturing, and the read image data d is, for example, as shown in FIG. It can be configured to detect that radiation irradiation has started when a predetermined threshold value dth is exceeded.

  And when the control means 22 detects that the irradiation of radiation was started as described above, as shown in FIG. 17, the application of the on-voltage to each scanning line 5 is stopped at that time, An off voltage is applied from the gate driver 15b to all the lines L1 to Lx of the scanning line 5, each TFT 8 is turned off, and the electric charge generated in each radiation detecting element 7 due to radiation irradiation is stored in each radiation detecting element 7. To the charge accumulation state to be accumulated in.

  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. 17, the line Ln of the scanning line 5) is to be applied (the line Ln + 1 of the scanning line 5 in the case of FIG. 17). 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 main image data D.

  Note that it is also possible to perform the reading process of the main image data D by starting the application of the on-voltage from the first line L1 of the scanning line 5, for example.

  In addition, in the reading process of the image data d for irradiation start detection before radiographic imaging in the detection method 1 described above, the time during which the ON voltage is applied to each of the lines L1 to Lx of the scanning line 5, that is, a certain scanning line 5 On the other hand, it is possible to appropriately perform improvements such as increasing the detection sensitivity of the image data d for detecting the start of irradiation by increasing the time from the start of applying the on-voltage to the time when the applied voltage is switched to the off-voltage. Is possible.

[Detection method 2]
In addition, as in the detection method 1 described above, the reading process of the leak data dleak is repeatedly performed before the radiographic image capturing, instead of the configuration of performing the reading process of the irradiation start detection image data d before the radiographic image capturing. It can also be configured to do so.

  Here, as shown in FIG. 19, 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. 20, each reading circuit is supplied from the control means 22 in a state in which 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 for irradiation start detection, when the correlated double sampling circuit 19 transmits the pulse signal Sp1 from the control means 22, the voltage output from the amplifier circuit 18 at that time point. Holds the value Vin. Then, the charge q leaked from each radiation detection element 7 via each TFT 8 is accumulated in the capacitor 18b of the amplifier circuit 18 to increase the voltage value output from the amplifier circuit 18, and the pulse signal Sp2 is transmitted from the control means 22. Then, the correlated double sampling circuit 19 holds the voltage value Vfi output from the amplifier circuit 18 at that time.

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

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

  Therefore, as described above, when the leak data dleak is read out repeatedly before radiographic imaging, the scan voltage 5 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.

  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. 19) leaking from each radiation detection element 7 via each TFT 8 increases.

  Therefore, as shown in FIG. 22, the leak data dleak read at that time (in FIG. 22, 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). The leaked data dleak) read out is not shown in the figure, but is larger than the leaked data dleak read before that, as in FIG. 18 in the case of the image data d. In FIG. 22, “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 when dleak_th is exceeded.

  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 (the line L5 of the scanning line 5 in the case of FIG. 22) after the scanning line 5 to which the on-voltage is applied (in the case of FIG. 22, 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 the main image data D.

  Even in the case shown in FIG. 22, the main image data D can be read out by starting application of an on-voltage from, for example, the first line L <b> 1 of the scanning line 5.

  Further, in the reading process of the leak data dleak in the detection method 2 described above, the detection sensitivity of the leak data dleak is increased by increasing the transmission interval of the pulse signals Sp1 and Sp2 transmitted to the correlated double sampling circuit 19, etc. Improvements can be made as appropriate.

[Processing in a radiographic imaging device in a series of radiographic imaging]
Next, under the configuration of the radiographic image capturing apparatus 1 that captures still images (that is, individual radiographic images p, the same applies hereinafter) as described above, there is movement such as the expansion and contraction of the respiratory organ described above. A process in the radiographic image capturing apparatus 1 in the case of performing a series of radiographic image capturing on an organ or the like and performing semi-moving image capturing will be described. Hereinafter, the operation of the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 according to the present embodiment will also be described.

  In the case where a series of radiographic imaging is performed in a semi-moving manner, in the present embodiment, radiography is continuously performed from the console 58 (see FIGS. 11 and 12) to the radiographic imaging apparatus 1 (that is, semi-moving) A signal indicating that the process is to be performed and information on the number of times of radiation irradiation are transmitted. Note that only a signal indicating that imaging is continuously performed is transmitted from the console 58, and when a series of imaging is completed, a signal indicating that imaging is completed is transmitted from the console 58 to the radiographic imaging apparatus 1. It is also possible to configure as described above.

  In the case of single imaging, the radiographic image capturing apparatus 1 immediately enters a mode for performing offset data O readout processing, which will be described later, after the readout processing of the main image data D is completed as described above. When the signal indicating that the shooting is continuously performed as described above is received, the offset data O is not immediately read out after the shooting and the following processing is performed. Yes.

  That is, as shown in FIG. 23, in the radiographic image capturing apparatus 1, in the case of the cooperative method described above, the reset processing of each radiation detection element 7 is performed before radiographic image capturing, and in the case of the non-cooperative method, Before image capturing, reading processing of image data d for detection of irradiation start and leak data dleak is performed. Then, when the first radiation irradiation is started, the state shifts to a charge accumulation state, and thereafter, reading processing of the main image data D is performed.

  Then, when the reading process of the main image data D is finished, the reading process of the offset data O, which will be described later, is not performed, and the reset process of each radiation detection element 7 (in the case of the cooperation method), the image data d for detecting the start of irradiation, The reading process of leak data dleak (in the case of a non-cooperative system) is resumed. When the second irradiation is performed, the second main image data D is read out through the charge accumulation state.

  In this way, for each imaging, in the case of the cooperative method, each process of the reset process of each radiation detection element 7 → the charge accumulation state → the reading process of the present image data D is also performed in the case of the non-cooperative method. Each process of reading out image data d or leak data dleak → charge accumulation state → reading processing of main image data D is continuously performed until a predetermined number of radiation irradiations are completed.

  In this embodiment, after a series of radiographic image capturing is completed, the main image data D obtained by each imaging is transmitted from the radiographic image capturing apparatus 1 to the console 58. .

  It should be noted that the main image data D can be transmitted to the console 58 after each shooting. This point will be described later. At this time, as will be described later, in the present embodiment, the main image data D is reversibly compressed and transmitted, but the compression method and the like will be described later.

  Furthermore, in the present embodiment, preview image data is transmitted after the first imaging, and the offset data O is read out after a series of radiographic imaging, which will be described later.

  On the other hand, in order to reproduce each still image obtained by a series of imaging as a semi-moving image on the image display device (or the display unit 58a of the console 58), when each radiographic image capturing device 1 captures each still image. It is necessary to accurately measure the actual time interval ΔT for each radiographic image capture.

  And in this embodiment, new means and apparatuses, such as an additional function module described in patent document 4 mentioned above, are not provided in the radiographic imaging apparatus 1, but the function already installed in the radiographic imaging apparatus 1. Each elapsed time is measured using a unit, that is, specifically, the control means 22.

  At that time, in order to measure the time interval ΔT for each radiographic image capture, it is necessary to set a reference time point for each radiographing. Therefore, for example, when imaging is performed in a cooperative manner as described above, an interlock release signal is transmitted from the radiographic image capturing apparatus 1 to the radiation generating apparatus 55 and the charge accumulation state is reached, or When imaging is performed in a non-cooperative manner, the control unit 22 of the radiographic imaging device 1 detects the start of radiation irradiation based on the read image data d for starting irradiation detection and leak data dleak. Can be set.

  That is, as the time interval ΔT for each radiographic image capturing in a series of radiographic image capturing, the time interval ΔT between the time points when the radiographic image capturing is shifted to the charge accumulation state, or the time point when the radiation irradiation start is detected Can be configured to measure each of the time intervals ΔT. In the non-cooperative system, since the transition to the charge accumulation state is made as soon as the start of radiation irradiation is detected, these timings are almost simultaneously. In other words, even in the non-cooperation method, it is possible to measure each time interval ΔT between the time points when the state is shifted to the charge accumulation state.

  Further, in the present embodiment, as described above, it is configured so that photographing can be performed by any of the cooperation method and the non-cooperation method, and the reading process of the main image data D is always performed in any method. Done. Therefore, in this embodiment, in order to make it possible to unify and grasp the time points at which each radiographic image is taken in any method, in this embodiment, as shown in FIG. The time when the reading process of D is started is set as the time when each radiographic imaging is performed.

  When configured in this manner, the time point when the reading process of the main image data D is started is different from the time point when the radiation image capturing apparatus 1 is irradiated with radiation. However, after the radiation irradiation is started as described above, the state shifts to the charge accumulation state, and the reading process of the main image data D is started after a predetermined time. For this reason, the time interval ΔT from when the reading process of the main image data D is started after a certain number of shootings to when the reading process of the main image data D is started after the next shooting is a radiation at the time of the shooting. The time interval is the same as the time interval from the start of irradiation until the start of radiation irradiation at the next imaging.

  Therefore, as in the present embodiment, even when the time point when the reading process of the main image data D is started in each radiographic image capturing is set as the time point when each radiographic image capturing is performed, It is possible to accurately measure the actual time interval ΔT for each photographing when a still image is photographed.

  Therefore, in the present embodiment, the control unit 22 of the radiographic image capturing apparatus 1 starts from the time point when the reading process of the main image data D is started in each radiographic image capture, and the time interval ΔT between the time points in each radiographing operation. Is to measure each.

  Specifically, the control unit 22 resets the counter at the time when the reading process of the main image data D is started in the first radiographic imaging, and starts measuring the count corresponding to the elapsed time from that time. . Then, the control means 22 increases the count number of the counter by one for every predetermined number of clocks, for example.

Then, the control means 22 stores the counter count in the memory as the time interval ΔT _1,2 between the first and second imaging immediately before starting the reading process of the main image data D in the second radiographic imaging. Remember. Then, the counter is reset, and the reading process of the main image data D in the second shooting is started. Then, counting of the count corresponding to the elapsed time from that time is restarted.

  In the present embodiment, the control unit 22 thus performs a time interval from the previous (k−1) -th shooting to the current (k-th) shooting at every time when the reading process of the main image data D is started. ΔTk-1, k is stored in memory.

  If comprised in this way, even if it does not provide an additional function module etc. newly in the radiographic imaging device 1, in the radiographic imaging device 1, it will move like a lung etc. which expands and contracts whenever breathing. A certain subject can be accurately photographed as a quasi-moving image. Further, it is possible to accurately measure the time interval ΔTk−1, k for each photographing in which a plurality of still images constituting a quasi-moving image are photographed by the radiation image photographing apparatus 1.

  In addition, as described above, instead of measuring the time interval ΔT between the time points when the reading process of the main image data D is started as the time interval ΔT for each radiographic image capturing in a series of radiographic image capturing, the main image data It is also possible to configure to measure the time interval ΔT between the time points when the D reading process is completed.

  Even with this configuration, as described above, the time for each radiographic image capture is based on the read processing of the main image data D that is always performed regardless of whether the radiographing is performed using the cooperative method or the non-cooperative method. It is possible to accurately measure the interval ΔT, and it is possible to accurately measure the time interval ΔT for each imaging in which a plurality of still images constituting a quasi-moving image are captured by the radiation image capturing apparatus 1.

[Transmission of preview image data, etc.]
Even if radiographic imaging is performed as described above, there is a possibility that the subject has not been accurately captured. If a series of radiographic image capturing operations are continued even though the subject is not accurately captured, the multiple times of radiation applied to the subject patient are wasted. Then, since re-imaging is necessary, the patient has to irradiate the radiation a plurality of times and perform a series of imaging, and the patient's exposure dose increases.

  Further, in the radiographic image capturing apparatus 1, although the subject is not accurately captured, a wasteful process is continued by repeating the reading process of the main image data D in a series of radiographic image capturing. Thus, there arises a problem that the power of the battery 24 (see FIG. 7 and the like) is consumed.

  Therefore, in the present embodiment, although not shown in FIG. 23, the control unit 22 of the radiographic image capturing apparatus 1 is read out by the first radiographic image capturing among the above-described series of plural radiographic image capturing. Data for a preview image is created based on the main image data D and transmitted to the console 58. Note that the preview image data is not created or transmitted for the main image data D read in the second and subsequent shootings.

  Specifically, the control means 22 of the radiographic image capturing apparatus 1 reads out the main image data D from each of the radiation detection elements 7 in the first radiographic image capture among a plurality of radiographic image captures. Thinned data Dt is created by thinning data at a predetermined rate from the inside.

  For example, as shown in FIG. 24, main image data D read from the radiation detection element 7 (m, n) in the m-th row and the n-th column of the detection unit P (see FIGS. 4 and 7) is represented by D (m, When represented by n), the control means 22 predetermines a predetermined number from the main image data D (m, n) read out in the first shooting, for example as shown by hatching in FIG. Main image data read from each radiation detection element 7 connected to the scanning line 5 designated at a ratio of one for each of the lines L1 to Lx of the scanning lines 5 (four in the case of FIG. 25). D (m, n) is extracted and used as thinned data Dt.

  The control unit 22 transmits the extracted thinned data Dt to the console 58 as preview image data.

  In this case, for example, all the main image data D may be read and stored in the storage unit 23 (see FIG. 7 and the like), and then only the thinned data Dt may be read from the storage unit 23 and transmitted. Further, when the main image data D is read out and stored in the storage means 23 for each of the lines L1 to Lx of the scanning line 5 in the reading process of the main image data D, the main image of the designated scanning line 5 is read. The data D can be stored in the storage means 23 and transmitted to the console 58 at the same time.

  In this case as well, when the thinned data Dt is transmitted to the console 58 as preview image data, the thinned data Dt is compressed and transmitted. This will be described later.

  On the other hand, in the present embodiment, when the preview image data is transmitted from the radiation image capturing apparatus 1 as described above, the console 58 generates the preview image p_pre based on the data and displays the generated preview image p_pre. It is displayed on the part 58a.

  Then, the radiologist viewing the displayed preview image p_pre determines that the subject is not properly captured in the image and needs to be re-photographed, and denies the preview image p_pre to the console 58 In a case where the console 58 has been performed (that is, an operation indicating that the preview image p_pre is not approved), the console 58 performs a series of a plurality of radiographic imaging currently performed on the radiographic imaging apparatus 1. Processing (see FIG. 23) is stopped.

  When receiving the stop signal from the console 58, the radiographic image capturing apparatus 1 stops a series of processes, discards the read main image data D, and returns to the initial state. That is, the reset processing (in the case of a cooperative method) of each radiation detection element 7 shown in the leftmost part of FIG. 23 or the reading process of image data d and leak data dleak for detecting the start of irradiation (in the case of a non-cooperative method). It returns to the state to do.

  With this configuration, in the radiographic imaging apparatus 1, useless reading processing of the main image data D is repeated, the battery 24 is consumed, and the patient exposure dose increases to increase the burden on the patient. This can be prevented accurately.

  In the present embodiment, when a radiographer who has viewed the preview image p_pre performs an operation for approving the preview image p_pre (specifically, an operation such as clicking an “OK” button displayed on the screen). The console 58 does not perform any control on the radiographic image capturing apparatus 1. The radiographic image capturing apparatus 1 continues a series of processes (see FIG. 23) in a series of radiographic image captures currently being performed.

[Processing after a series of radiographic images]
When a series of radiographic imaging is performed as described above (see FIG. 23), the control unit 22 of the radiographic imaging apparatus 1 performs each imaging obtained by the series of radiographic imaging. The main image data D is transmitted to the console 58. At this time, in the present embodiment, the time interval ΔT measured for each shooting and stored in the memory is read out, and the information of each time interval ΔTk−1, k is associated with each corresponding main image data D and console. 58 is transmitted.

  That is, the main image data D obtained by the k-th shooting is transmitted to the console 58 in association with the time interval ΔTk-1, k from the (k-1) -th shooting to the k-th shooting. Yes.

  As a method of associating the time interval ΔT with the corresponding main image data D, for example, one of the following two methods can be employed.

[Association Method 1]
For example, when transmitting the main image data D (actually the main image data D compressed as will be described later; the same applies hereinafter) to the console 58, the information of the time interval ΔT is used as the header of the corresponding main image data D. Each part can be written and transmitted to the console 58.

  The same applies to the following matching method 2, but in this case, as the information of the time interval ΔT, the count number of the counter (that is, the clock number in the above case) measured by the control means 22 is used as the header. It is also possible to configure so as to write in the part, and it is also possible to convert the count number of the counter into units of seconds and to write the converted number of seconds in the header part.

[Association method 2]
In addition, when the radiographic image capturing apparatus 1 captures a diagnostic radiographic image p as described above, an important subject portion such as a lesion is usually captured in a central portion or the like of the radiographic image p. In other words, an important subject portion such as a lesion is usually not photographed at the peripheral portion of the radiation image p.

  Therefore, as shown in FIG. 26, for example, in each main image data D obtained by the k-th radiographic image capturing, a predetermined pixel (ie, radiation detection element 7) portion corresponding to the peripheral portion of the radiographic image p, or the like. It is possible to delete the main image data D of the pixel portion, write information of the time interval ΔTk−1, k into the pixel portion, and transmit the information to the console 58.

  Even in such a configuration, in most cases, the main image data D of the pixel portion where the lesion is photographed is not deleted, and the console does not adversely affect important subject information such as the lesion. It is possible to transmit the information of the time interval ΔT to 58.

  It should be noted that, as in the association methods 1 and 2 described above, information on the time interval ΔT is written in the header portion, or whether the predetermined image portion such as the peripheral portion of the radiation image p is the main image data D. By writing the data as described above and transmitting it to the console 58, the control configuration in the conventional radiographic image capturing apparatus 1 that captures only a still image, the data configuration when transmitting the main image data D, etc. to the console 58 are large. The information of the time interval ΔT can be transmitted to the console 58 without any change.

[Compression processing of image data D]
Here, a compression process of the image data D when the image data D is transmitted from the radiation image capturing apparatus 1 to the console 58 will be described.

  As described above, when the radiographic image capturing apparatus 1 captures a diagnostic radiographic image p, if the main image data D is irreversibly compressed and transmitted to the console 58, a lesion or the like captured in the radiographic image p is detected. An important subject portion may not be completely restored, which may hinder diagnosis. Therefore, in the present embodiment, the control unit 22 of the radiographic image capturing apparatus 1 performs reversible compression (also referred to as lossless compression) on the main image data D and transmits it to the console 58.

  As a lossless compression method, for example, a method such as Huffman coding, LZ78, or arithmetic coding can be used.

  Further, for example, in order to examine the distribution of the main image data D (m, n) (see FIG. 24) read from each radiation detection element 7 (m, n) in a certain shooting, each main image data Vote D (m, n) on the histogram. Then, the distribution of the appearance frequency F of each main image data D is usually in a state where the distribution shape is different for each imaging region (that is, the body part of the patient as the subject) as shown in FIGS. 27 and 28, for example. .

  When the main image data D (m, n) having such a distribution is reversibly compressed by, for example, Huffman coding, the normal image data shown in FIG. 29 is used for the main image data D (m, n), for example. A Huffman dictionary (that is, a Huffman code table, also referred to as a coding dictionary) created based on the distribution is assumed, and a Huffman code Hc is assigned to each main image data D. However, the compression rate does not necessarily increase.

  That is, since the ratio of the main image data D to which the relatively long Huffman code Hc is assigned increases in each read main image data D (m, n), the main image data D is transmitted as it is without being compressed. There are cases where the amount of data to be transmitted is not so small compared to the case where it is performed. Therefore, when Huffman coding is performed by assigning the Huffman code Hc to the main image data D, the data transmission time may not necessarily be shortened compared to the case where the main image data D is transmitted without being compressed. .

  On the other hand, the inventors of the present application have calculated the difference ΔD between the main image data D (m, n) and performed compression processing by Huffman coding on the difference ΔD, thereby reducing the data compression rate. It has been found that the data transmission time can be shortened. Hereinafter, specific compression processing by such a method will be described with reference to two methods.

[Compression method 1]
First, compression method 1 which is the first compression method will be described. This compression method 1 is a case where the compression method described in detail in the pamphlet of International Publication No. 2011/010480, Japanese Patent Application Laid-Open No. 2011-87727, etc. previously submitted by the applicant of the present application is used as the compression processing. For details, refer to those publications. A brief description is given below.

  In the compression method 1, first, as shown in FIG. 24, for the main image data D (m, n) read from each radiation detection element 7 (m, n) in a certain shooting, the signal line 6 Each radiation detection element 7 adjacent to each other in the extending direction (vertical direction in FIG. 24; hereinafter referred to as a signal line direction) and the extending direction of the scanning lines 5 (lateral direction in FIG. 24; hereinafter referred to as the scanning line direction). A difference ΔD between the main image data D (m, n) read from (m, n) is calculated.

That is, when configured to calculate the difference ΔD in the signal line direction,
ΔD (m, n) = D (m, n) −D (m−1, n) (1)
When calculating the difference ΔD by the above, and calculating the difference ΔD in the scanning line direction,
ΔD (m, n) = D (m, n) −D (m, n−1) (2)
To calculate the difference ΔD.

  When each difference ΔD between the main image data D (m, n) adjacent in the signal line direction and the scanning line direction calculated in this way is voted on the histogram, as shown in FIG. 30, the appearance of each difference ΔD. Unlike the case of the main image data D shown in FIGS. 27 and 28, the distribution of the frequency F becomes a normal distribution distribution in a relatively narrow range centering on ΔD = 0 regardless of the imaging region.

  Therefore, a Huffman dictionary is created in advance based on, for example, the normal distribution shown in FIG. And each difference (DELTA) D is calculated with respect to this image data D obtained by each imaging | photography according to said (1) Formula or (2) Formula. Then, a Huffman dictionary is applied to each calculated difference ΔD to assign a Huffman code Hc.

  Then, as described above, the distribution of the appearance frequency F of the difference ΔD becomes a distribution as illustrated in FIG. Since the appearance frequency F of ΔD is small, the data compression rate is high.

  Therefore, it is possible to accurately reduce the data transmission time by transmitting each compressed difference ΔD, that is, each Huffman code Hc, as compared to the case where the main image data D is transmitted without being compressed. .

  In the case of the above formulas (1) and (2), when calculating the difference ΔD (1, n) or the difference ΔD (m, 1), as can be seen from FIG. Since the values of (0, n) and D (m, 0) do not exist, the above calculation cannot be performed. Therefore, in the present embodiment, predetermined values are assigned in advance as the values of D (0, n) and D (m, 0), respectively.

  Further, as described above, the thinned data Dt created by thinning out the data at a predetermined rate from the main image data D read out at the first photographing as shown in FIG. In the case of transmitting to the console 58 as well, it is possible to compress the data for the preview image using the compression method 1 and transmit it.

  That is, for example, when the preview image data extracted as shown in FIG. 25 is virtually collected, the state shown in FIG. 31 is obtained. In this state, the difference ΔD between the preview image data adjacent in the signal line direction (vertical direction in the figure) or the scanning line direction (horizontal direction in the figure) is calculated.

  Then, a Huffman dictionary similar to the above or a Huffman dictionary created for preview image data is applied to each calculated difference ΔD, and a Huffman code Hc is assigned to each difference ΔD. If the preview image data is compressed and transmitted in this manner, the transmission time of the preview image data can be accurately shortened as described above.

[Compression method 2]
In the compression method 1 described above, one frame (that is, one surface of the detection unit P (see FIGS. 4 and 7) in which each radiation detection element 7 (m, n) is arranged) read out by one imaging. The difference ΔD between the main image data D (m, n) of the radiation detection elements 7 (m, n) adjacent to each other in the signal line direction or the scanning line direction was calculated.

  On the other hand, for each individual radiation detection element 7, a difference ΔDk−1, k between the main image data D read out in a series of a plurality of radiographic images is calculated, and the difference ΔDk−1, k is calculated with respect to the difference ΔDk−1, k. The Huffman dictionary can be applied.

That is, as shown in FIG. 32, for example, when viewing the radiation detection element 7 (m ^* , n ^* ), the main image data Dk-1 (m ^* , n ^* ) read out in the (k-1) th imaging. And ΔDk−1, k (m ^* , n ^* ) between the image data Dk (m ^* , n ^* ) read out in the k-th shooting,
ΔDk-1, k (m ^* , n ^* ) = Dk (m ^* , n ^* ) − Dk−1 (m ^* , n ^* ) (3)
Is calculated by

  Then, the calculation of the expression (3) is read for each radiation detection element 7 (m, n) by the main image data D (m, n) read in each shooting and the previous shooting. This is performed between the actual image data D (m, n).

  When each difference ΔDk-1, k calculated in this way is voted on the histogram, the distribution of the appearance frequency F of each difference ΔDk-1, k is similar to the distribution of the difference ΔD shown in FIG. Therefore, the distribution is a normal distribution in a relatively narrow range centering on ΔDk−1, k = 0, irrespective of the imaging region. Therefore, by creating a Huffman dictionary in advance based on such a distribution and applying it to the calculated differences ΔDk−1, k, the data compression rate is increased, and the data transmission time is increased. Can be shortened.

  In this case, the main image data D1 (m, n) read in the first shooting cannot be assumed to be the previous shooting, so the difference ΔD0,1 (m, n) is calculated. I can't. Therefore, when this compression method 2 is adopted, at least the main image data D1 (m, n) read in the first shooting is adjacent in the signal line direction or the like using the compression method 1 described above, for example. The difference ΔD between the main image data D of the radiation detecting element 7 is compressed and transmitted to the console 58.

  Further, when the above-described [Association Method 1] is adopted, the information of the time interval ΔT (see FIG. 23) is written in the header portion of the corresponding data and transmitted to the console 58. The time interval ΔT is written and transmitted in the header portion of the difference ΔD and the difference ΔDk−1, k compressed by the compression method 1 and the compression method 2.

  Furthermore, when the above [Association method 2] is adopted, the information on the time interval ΔT written in the predetermined pixel portion of the main image data D (see FIG. 26) is also adjacent by the compression method 1 described above. The difference ΔD of the pixel (radiation detection element 7) from the main image data D is calculated, or the difference ΔDk−1 from the previous time interval ΔT written in the main image data D of the previous photographing by the compression method 2 described above. , k can be calculated, and the compressed data can be transmitted.

  Further, with respect to the information of the time interval ΔT written in the predetermined pixel portion of the main image data D, the difference ΔD and the difference ΔDk−1, k are not calculated and are transmitted to the console 58 without being compressed. Also good.

[About sending data after each shooting]
On the other hand, in the present embodiment, as described above, after a series of radiographic image capturing is completed, each main image data D read out in each imaging is reversibly compressed as described above to generate a radiographic image. It is transmitted from the photographing apparatus 1 to the console 58.

  However, the number of imaging performed in a series of radiographic imaging (ie, the number of radiographic images p), the number of each radiation detection element 7 (ie, the number of pixels) arranged in the detection unit P, etc., and the storage means 23 (FIG. 7). Etc.), all of the main image data D read out in a series of radiographic imaging may not be stored in the storage means 23.

  Therefore, in such a case, each time the main image data D is read out in each series of radiographic image capturing, the compression processing of the differences ΔD and ΔDk−1, k by the compression method 1 and the compression method 2 described above. And the compressed differences ΔD, ΔDk−1, k can be transmitted to the console 58.

  In this case, the main image data D read in the subsequent shooting is overwritten and saved on the main image data D read in the previous shooting in the storage unit 23. If comprised in this way, the memory | storage means 23 will be enough if it has a storage capacity which can preserve | save the main image data D for several frames.

[About offset data read processing]
Further, in the present embodiment, after a series of radiographic image capturing is completed, the offset data O reading process is performed thereafter. In this embodiment, the offset data O reading process is performed by the same processing sequence as a processing sequence for one time in a series of radiographic image capturing.

  Specifically, in the present embodiment, as described above, the cooperation method (see FIG. 15 and the like) or the non-cooperation method (see the detection method 1 shown in FIG. 17 and the detection method 2 shown in FIG. 22 and the like). Each radiographic image is taken.

  For example, when each radiographic image capturing is performed in a cooperative manner, as shown in FIG. 33, after the final reading process of the main image data D is completed, the offset data O reading process is performed. In the offset data O readout process, a series of processing sequences from the reset process of each radiation detection element 7 before radiographic imaging to the readout process of the main image data D through the charge accumulation state (see FIG. 15 and the like). ) Is repeated to perform the offset data O reading process.

  The same applies to the following non-cooperative methods, but in this case, no radiation is irradiated to the radiation image capturing apparatus 1 in the charge accumulation state.

  Although not shown, for example, when each radiographic image is taken in a non-cooperative manner, the reading process of the offset data O is performed after the final reading process of the main image data D is completed. .

  In the offset data O reading process, the reading process of the image data d for irradiation start detection before the radiographic image capturing (see FIG. 17 and the like), the reading process of the leak data dleak, and the reset process of each radiation detecting element 7 ( After the process is performed, the same process sequence as the process of reading the main image data D through the charge accumulation state is repeated, and the process of reading the offset data O is performed. ing.

  Then, the control means 22 of the radiographic image capturing apparatus 1 applies, for example, the signal line direction and the like to each offset data O read for each radiation detection element 7 by the offset data O reading process by the compression method 1 described above. The difference ΔO between the offset data O of the radiation detection elements 7 adjacent to the image is calculated, each difference ΔO is reversibly compressed by Huffman coding or the like, and transmitted to the console 58.

[Console processing]
Next, processing in the console 58 will be described.

  In the present embodiment, as described above, the console 58 compresses each difference (that is, the Huffman code Hc) regarding the thinned data Dt (see FIGS. 25 and 31) as data for the preview image from the radiographic image capturing apparatus 1. Is decompressed, and each thinned-out data Dt as shown in FIG. 31 is restored.

  A preview image p_pre is generated based on the restored thinning data Dt, and the generated preview image p_pre is displayed on the display unit 58a (see FIGS. 11 and 12). Note that the radiologist performs an operation to approve or deny the approval based on the preview image p_pre displayed on the display unit 58a, and processing in the console 58 or the like when the operation is performed is as described above. is there.

  On the other hand, when the console 58 receives the compressed difference ΔD or the compressed difference ΔDk−1, k (that is, the Huffman code Hc) from the radiation image capturing apparatus 1, each of the compressed differences ΔD, etc. To restore the original differences ΔD and the like. For this reason, the console 58 is provided with the same Huffman dictionary as the Huffman dictionary included in the radiation image capturing apparatus 1.

  Then, the console 58 restores the original main image data D by adding the original difference ΔD that has been decompressed and restored and the original image data D that has already been restored.

Specifically, for example, when the control unit 22 of the radiographic image capturing apparatus 1 calculates and compresses the difference ΔD in the signal line direction by the compression method 1 described above, the console 58 first has a predetermined value D assigned thereto. (0, n) and the expanded difference ΔD (1, n) are added according to the following equation (4) which is the inverse operation of the above equation (1) to obtain the original main image data D (1, n) To restore.
D (1, n) = D (0, n) + ΔD (1, n) (4)

  Subsequently, when the difference ΔD (2, n) is expanded, the original image data D (1, n) restored as described above and the expanded difference ΔD (2, n) are added in the same manner as described above. Then, the original main image data D (2, n) is restored.

In this way, every time the difference ΔD (m, n) is expanded, the restored original image data D (m−1, n) and the expanded difference ΔD (m, n) are converted into the above (1). The original original image data D (m, n) is restored by performing addition according to the following equation (5) which is the inverse operation of the equation.
D (m, n) = D (m-1, n) + ΔD (m, n) (5)

Similarly, for example, when the control means 22 of the radiographic image capturing apparatus 1 calculates and compresses the difference ΔD in the scanning line direction by the compression method 1 described above, the console 58 is similarly assigned with a predetermined value D. (M, 0) and the original image data D (m, n−1) (or D (m, 0)) already restored according to the following formula (6) which is the inverse operation of the formula (2). The expanded difference ΔD (m, n) is added one after another to restore the original main image data D (m, n).
D (m, n) = D (m, n−1) + ΔD (m, n) (6)

  Further, for example, when the control unit 22 of the radiographic image capturing apparatus 1 calculates and compresses the difference ΔDk−1, k by the compression method 2 described above, the console 58 displays each main image obtained by the first imaging. For the data D (m, n), the original main image data D (m, n) is restored as described above.

The console 58 then expands the difference ΔDk−1 for each radiation detection element 7 (m, n) for the main image data Dk (m, n) obtained in the second and subsequent k-th imaging. k and the restored original image data Dk-1 (m, n) obtained by the (k-1) th shooting are added according to the following equation (7), which is the inverse operation of the above equation (3): The original main image data Dk (m, n) is reconstructed.
Dk (m, n) = Dk-1 (m, n) +. DELTA.Dk-1, k (m, n) (7)

  Further, the console 58 similarly performs decompression processing and restoration processing on the compressed data related to the offset data O transmitted from the radiation image capturing apparatus 1 (that is, each difference ΔO described above), and thereby each radiation detection element 7. The original offset data O is restored every time.

Then, the console 58 subtracts the offset data O from the main image data D for each restored main image data D to calculate the so-called true image data D ^* , and the calculated true image data D ^* . On the other hand, processing such as gain correction, offset correction, defective pixel correction, gradation processing corresponding to the imaging region, and the like are performed, and a final radiographic image p is generated for each imaging of a series of radiographic imaging. ing.

  On the other hand, in the present embodiment, when the console 58 generates the radiographic image p for each imaging of the series of radiographic images as described above, it becomes the basis for each generated radiographic image p. Information of the time interval ΔT associated with each main image data D is associated with each other.

  That is, the console 58 sets the time interval ΔTk−1 associated with the k-th main image data D that is the basis of the radiographic image p captured at the kth time in a series of a plurality of radiographic images. , k (see FIG. 23 and FIG. 26) are associated with each other.

  At this time, for example, as in the case of [Association Method 1], information of the time interval ΔT corresponding to the header portion of each radiation image p may be written. Further, for example, as in the above [Association method 2], it is possible to write the information of the time interval ΔT in a predetermined pixel portion such as the peripheral portion of each radiation image p.

  In any case, the specific association method corresponds to the method required by the image display device (or console 58) side that reproduces each radiographic image p obtained by a series of imaging, that is, each still image in a semi-moving manner. Attached.

  Then, by associating each still image with the time interval ΔT in this way, the image display device can expand or contract by reproducing each still image according to the time interval ΔT associated with each still image. The movement of organs such as lungs can be reproduced at the time interval ΔT taken by the radiographic imaging device 1, and each still image obtained by a series of radiographic imaging is accurately displayed in a semi-moving manner. Is possible.

  As described above, according to the radiographic image capturing system 50 according to the present embodiment, the time for each radiographic image capturing when a series of plural radiographic image capturing is performed by the control unit 22 of the radiographic image capturing apparatus 1. Each interval ΔT is measured, and information on each measured time interval ΔT is transmitted to the console 58 in association with each corresponding main image data D or compressed data of the difference ΔD. Further, the console 58 associates each radiation image p generated based on the main image data D with information on each time interval ΔT associated with each main image data D.

  Therefore, unlike the conventional radiographic image capturing apparatus, even if an additional function module for capturing a moving image is not provided in the housing 2, the control means 22 simply measures the time interval ΔT of each image capturing, It is possible to accurately acquire information on the display time interval ΔT when each radiographic image p obtained by imaging, that is, each still image is displayed in a semi-moving manner.

  Therefore, it is possible to accurately capture a moving subject or the like as a quasi-moving image using the conventional radiographic image capturing apparatus 1 that captures only a still image. Further, it is not necessary to modify the radiation generator 55 (see FIGS. 11 and 12) to measure the time interval ΔT, and the time interval ΔT can be measured on the radiation imaging apparatus 1 side. .

  In addition, the console 58 corresponds to the main image data D that is the basis of each radiographic image p to each radiographic image p generated based on the main image data D obtained by each radiographic image capturing, that is, each still image. The information of the time interval ΔT that has been attached is associated with each other.

  Therefore, the image display device (or console 58) that reproduces each radiographic image p obtained by a series of radiographs, that is, each still image in a semi-moving manner, displays each still image in accordance with the time interval ΔT associated with each still image. By reproducing, it is possible to reproduce the movement of an organ such as the lung that expands and contracts at the time interval ΔT imaged by the radiographic image capturing apparatus 1.

  Therefore, by associating the information of the time interval ΔT with each still image on the console 58, it is possible to display each still image obtained by a series of radiographic image captures accurately and semi-movably on the image display device. Become.

  In addition, when irradiating the radiation from the radiation source 52 (see FIGS. 11 and 12) of the radiation generating device 55 in order to take the quasi-moving image, the radiologist operates the exposure switch 56 every time to irradiate the radiation. Alternatively, the radiation generating device 55 may be configured to automatically emit radiation from the radiation source 52 at a predetermined timing.

  In any of these cases, the radiographic imaging apparatus 1 according to the above embodiment accurately measures the time interval ΔT for each radiographic imaging in a series of radiographic imaging in the radiographic imaging apparatus 1. .

DESCRIPTION OF SYMBOLS 1 Radiation imaging device 5 Scanning line 6 Signal line 7, (m, n) 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 52 Radiation Source 55 Radiation Generator 58 Console 58a Display Unit D Main Image Data (Image Data)
d Image data for start of irradiation dleak Leak data dleak_th threshold Dt Thinned out data dth threshold P detection unit p radiation image p_pre preview image q charge r small area ΔD, ΔDk-1, k difference ΔT time interval

Claims (10)

A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other, and a plurality of radiation detection elements arranged in a two-dimensional manner in each small region partitioned by the plurality of scanning lines and the plurality of signal lines A detection unit comprising:
Scan driving means for applying an on voltage or an off voltage to each of the scanning lines;
Switch means connected to each of the scanning lines and causing the signal lines to discharge charges accumulated in the radiation detection element when an on-voltage is applied;
A readout circuit that converts the electric charge emitted from the radiation detection element into image data and reads the image data;
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 capable of communicating with an external device;
A radiographic imaging device comprising:
A radiation generator comprising a radiation source for irradiating the radiation imaging apparatus with radiation;
A console that generates a radiographic image based on the image data transmitted from the radiographic imaging device;
With
The control means of the radiographic imaging device measures a time interval for each radiographic imaging when a series of radiographic imaging is performed, and obtained by the series of radiographic imaging When transmitting each image data to the console, the information of each time interval is associated with each corresponding image data and transmitted to the console,
The console associates each time interval information associated with each image data with each radiation image generated based on the image data transmitted from the radiation image capturing apparatus. Radiation imaging system. The control means of the radiographic image capturing apparatus includes:
While radiation is being emitted from the radiation source of the radiation generator, an off voltage is applied to the scanning lines from the scanning drive means to accumulate charges generated by radiation irradiation in the radiation detection elements. It is configured to make a transition to the charge accumulation state to be performed, and then to perform a reading process of the image data from each of the radiation detection elements,
As the time interval for each radiographic image capturing, the time interval between the time points when the image data reading process is started or the time point when the image data reading process is completed in each time radiographic image capturing, or each time of radiation imaging The radiographic image capturing system according to claim 1, wherein a time interval between the time points when the state is shifted to the charge accumulation state in image capturing is measured. The control means of the radiographic imaging device writes the information of each time interval in the header portion of each corresponding image data and transmits it to the console,
The console reads the information on the time interval written in the header portion of each transmitted image data, and associates the read information on each time interval with each generated radiographic image. The radiographic imaging system according to claim 1 or 2. The control means of the radiographic imaging apparatus writes the information of each time interval to a predetermined pixel portion of each corresponding image data and transmits it to the console,
The console reads the time interval information written in the predetermined pixel portion of the transmitted image data, and associates the read time interval information with the generated radiographic images. The radiographic image capturing system according to claim 1, wherein: The control means of the radiographic imaging device, for each radiographic imaging in the series of radiographic imaging,
Prior to radiographic image capturing, the leakage from the radiation detection elements via the switch means in a state where the scan drive means applies an off voltage to the scan lines to turn off the switch means. Leak data read processing for converting charge into leak data, and reset processing for each radiation detection element performed by sequentially applying an on-voltage from the scan driving means to the scan lines,
When it is detected that radiation irradiation has started when the read leak data exceeds a threshold value, an off voltage is applied to each scanning line from the scanning drive means to generate charges generated by radiation irradiation. 5. The read-out process of the image data from each of the radiation detection elements is performed after shifting to a charge accumulation state to be accumulated in the radiation detection elements. 6. Radiation imaging system. The control means of the radiographic imaging device, for each radiographic imaging in the series of radiographic imaging,
Prior to radiographic image capturing, an on voltage is sequentially applied to each scanning line from the scanning driving means to perform a reading process of the image data for detection of irradiation start,
When it is detected that radiation irradiation has started when the read image data exceeds a threshold value, an off voltage is applied to each scanning line from the scanning drive means to generate charges generated by radiation irradiation. 5. The read-out process of the image data as the main image from each of the radiation detection elements is performed after shifting to a charge accumulation state to be accumulated in the radiation detection elements. The radiographic imaging system according to one item.   The control means of the radiographic imaging apparatus reads or irradiates leak data before radiographic imaging as a time interval for each radiographic imaging when the series of radiographic imaging is performed. The radiographic imaging system according to claim 5 or 6, wherein a time interval between the time points when the start of radiation irradiation is detected in the start detection image data reading process is measured. The control means of the radiographic image capturing apparatus obtains thinned data obtained by thinning out data at a predetermined ratio from the image data read out in the first radiographic image capturing among the series of radiographic image capturing. , Send it to the console as preview image data,
The console displays a preview image on a display unit based on the thinning data, and if the preview image is denied, the console performs a series of processes in the series of radiographic image capturing on the radiographic image capturing apparatus. The radiographic imaging system according to claim 1, wherein the radiographic imaging system is stopped. The control means of the radiographic imaging device is configured to perform the next round of the image data read out in one radiographic imaging out of the series of radiographic imaging for each of the radiation detection elements. Calculating each difference with the image data read out by radiographic imaging, reversibly compressing each difference for each calculated radiation detection element, and transmitting to the console,
The console expands each compressed difference transmitted from the radiographic imaging device, and decompresses each of the radiation detection elements into the restored image data in a certain radiographic imaging. Each image read out for each of the radiation detection elements in the series of the plurality of radiation image capturing so as to restore the image data in the next radiation image capturing by adding the difference. 9. The radiographic image capturing system according to claim 1, wherein data is restored. A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other, and a plurality of radiation detection elements arranged in a two-dimensional manner in each small region partitioned by the plurality of scanning lines and the plurality of signal lines A detection unit comprising:
Scan driving means for applying an on voltage or an off voltage to each of the scanning lines;
Switch means connected to each of the scanning lines and causing the signal lines to discharge charges accumulated in the radiation detection element when an on-voltage is applied;
A readout circuit that converts the electric charge emitted from the radiation detection element into image data and reads the image data;
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 capable of communicating with an external device;
With
The control means measures a time interval for each radiographic image capture when a series of radiographic image captures are performed, and consoles the image data obtained by the series of radiographic image captures. When transmitting to the radiographic imaging apparatus, the information of each time interval is transmitted to the console in association with the corresponding image data.

Images