JP2014064077A - Radiographic image photographing system and radiographic image photographing device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiographic image photographing system capable of shortening a cycle time from the time when the current radiographic image photographing ends to the time when the next radiographic image photographing is enabled, and more quickly displaying a preview image.SOLUTION: A radiographic image photographing system 50 comprises a console 58 with a display unit 58a and a radiographic image photographing device 1 with compression transfer means 22. The compression transfer means 22 of the radiographic image photographing device 1: compresses preview image data Dp extracted from image data D on the basis of dictionary data α generated in advance; transfers the compressed data to the console 58; transfers dictionary data β for the image data for compressing the image data D necessary to generate a radiographic image p which was generated per radiographic image photographing on the basis of the image data D necessary to generate the radiographic image p, to the console 58; compresses the image data D necessary to generate the radiographic image p on the basis of the dictionary data β for the image data; and transfers the compressed data to the console 58.

Description

  The present invention relates to a radiographic imaging system and a radiographic imaging apparatus used therefor.

  A so-called direct-type radiographic imaging device that generates electric charges by a detection element in accordance with the dose of irradiated radiation such as X-rays and converts it into an electrical signal, or other radiation such as visible light with a scintillator A so-called indirect radiographic imaging device that converts an electromagnetic wave having a wavelength and then generates a charge in a photoelectric conversion element such as a photodiode according to the energy of the converted electromagnetic wave and converts it to an electrical signal (ie, image data). Have been developed. In the present invention, the detection element in the direct type radiographic imaging apparatus and the photoelectric conversion element in the indirect type radiographic imaging apparatus are collectively referred to as a radiation detection element.

  This type of radiographic imaging device is known as an FPD (Flat Panel Detector), and is conventionally configured as a so-called special-purpose machine that is integrally formed with a support base (see, for example, Patent Document 1). In recent years, a portable radiographic imaging apparatus in which a radiation detection element or the like is housed in a casing and can be carried has been developed and put into practical use (for example, see Patent Documents 2 and 3).

  In such a radiographic imaging apparatus, for example, as shown in FIG. 3 and the like, which will be described later, normally, a plurality of radiation detection elements 7 are arranged in a two-dimensional form (matrix) on the detection unit P, and each radiation detection element 7 is connected to switch means formed of thin film transistors (hereinafter referred to as TFTs) 8.

  In general, radiographic imaging is performed by irradiating radiation from the radiation source of the radiation generating apparatus to the radiographic imaging apparatus via the subject, that is, the body of the subject. In radiographic imaging, the gate driver 15b applies a turn-off voltage to each of the lines L1 to Lx of the scanning line 5, and the radiation imaging apparatus is irradiated with radiation while each TFT 8 is turned off. Electric charges generated in the radiation detection elements 7 are accumulated in each radiation detection element 7.

  Then, after the radiation irradiation to the radiographic image capturing apparatus is completed, an ON voltage is sequentially applied from the gate driver 15b to each of the lines L1 to Lx of the scanning line 5 so that each TFT 8 is sequentially turned on to detect each radiation by irradiation. Charges generated and accumulated in the element 7 are sequentially discharged to the signal lines 6 and read out as image data D by the readout circuits 17 respectively.

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

  By the way, when radiographic imaging is performed using such a radiographic imaging apparatus, radiographic imaging may have to be performed one after another as in, for example, chest X-ray imaging in a mass examination. In such imaging, an operator such as a radiologist performs the next imaging immediately after completing the imaging, that is, without being restricted by waiting for a predetermined time after the imaging. Is what you want.

  From such an operator to the radiographic imaging apparatus or the radiographic imaging system using the radiographic imaging apparatus, the time until the next imaging can be performed (hereinafter referred to as cycle time). )) As much as possible, and there is a request to make the time required for one shooting as short as possible.

  The present invention has been made in view of the above points, and a radiographic imaging system capable of shortening the cycle time from the end of radiographic imaging until the next imaging becomes possible, and radiation used therein An object is to provide an image photographing apparatus.

  In such a radiographic image capturing system, preview image data Dp extracted from the captured image is transferred to the console 58 (see FIGS. 4 and 5 described later) and previewed on the display unit 58a of the console 58 or the like. It is desirable to display the image p_pre as early as possible, determine whether or not the subject is properly captured in the image, and determine whether or not re-shooting is necessary as early as possible.

  Therefore, the present invention also aims to provide a radiographic image capturing system and a radiographic image capturing apparatus capable of reducing the cycle time as described above and displaying a preview image earlier. .

In order to solve the above-described problem, the radiographic imaging system of the present invention includes:
A plurality of scanning lines and a plurality of signal lines arranged to cross each other;
A plurality of radiation detection elements arranged two-dimensionally;
Scanning drive means for switching a voltage applied to each scanning line between an on-voltage and an off-voltage,
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 for reading out the electric charge emitted from the radiation detection element as image data;
Control means for controlling at least the scanning drive means and the readout circuit to read out the image data from each of the radiation detection elements;
A communication means capable of communicating with the console;
Compression transfer means for compressing and transferring data obtained by radiographic imaging to the console via the communication means;
A radiographic imaging device comprising:
The console including a display unit;
With
The compression transfer unit of the radiographic image capturing apparatus includes:
Preview image data is extracted from the read image data at a predetermined ratio, and the extracted preview image data is compressed based on preview dictionary data generated in advance and transferred to the console. With
Necessary for generating image data dictionary data for compressing the image data necessary for generating a radiographic image for each radiographic image capturing, transferring the image data dictionary data to the console, and generating the radiographic image Image data is compressed based on the image data dictionary data and transferred to the console,
The console is
When the preview image data is transferred from the radiographic image capturing apparatus, the preview dictionary data is the same as the previously generated preview dictionary data included in the radiographic image capturing apparatus. Decompressing the compressed preview image data based on the dictionary data for restoring the original preview image data, generating a preview image based on the decompressed preview image data, and displaying it on the display unit;
When the image data dictionary data and the image data necessary for generating the compressed radiation image are transferred from the radiation image capturing apparatus, the radiation image of the radiation image is transferred based on the transferred image data dictionary data. The image data necessary for generation is decompressed to restore the original image data, and a radiation image is generated based on the restored original whole image data.

  According to the radiographic image capturing system and radiographic image capturing apparatus of the system as in the present invention, for each radiographic image capture, for example, image data necessary for generating a radiographic image such as remaining image data other than preview image data. Thus, the image data dictionary data is generated by accurately matching the distribution of the actual frequency F of the image data necessary for generating the radiation image (see, for example, FIG. 13 described later).

  Therefore, it is possible to compress the image data necessary for generating the radiographic image in a state where the compression rate is maximized, and the data amount of the compressed image data can be further reduced. As a result, the time required to transfer the compressed image data can be further shortened, and the cycle time from when one image is taken until the next image can be taken is accurately reduced accordingly. Is possible.

  Further, when the preview image data is compressed and transferred, the preview dictionary data is not generated for each shooting as described above, but the preview image data is generated based on the preview dictionary data generated in advance. Compress and transfer to console. Therefore, after completion of the image data reading process in the radiographic imaging device, the preview image data is immediately extracted from the image data without generating the preview dictionary data, and based on the preview dictionary data generated in advance. Compressed and transferred.

  Therefore, compared to the case where the preview dictionary data is generated and then the preview image data is compressed and transferred based on the preview dictionary data, the time required for generating the preview dictionary data is eliminated. After the image data D reading process, it is possible to transfer the compressed preview image data to the console earlier, and to display the preview image earlier.

It is sectional drawing of a radiographic imaging apparatus. It is a top view which shows the structure of the board | substrate of a radiographic imaging apparatus. It is a block diagram showing the equivalent circuit of a radiographic imaging apparatus. It is a figure which shows the structural example of the radiographic imaging system which concerns on this embodiment constructed | assembled in the imaging | photography room. It is a figure which shows the structural example of the radiographic imaging system which concerns on this embodiment constructed | assembled on the round-trip vehicle. It is a figure explaining that each electric charge leaked from each radiation detection element via each TFT is read as leak data. It is a graph showing the example of the time transition of the leak data read. It is a timing chart explaining the timing etc. which apply an ON voltage to each scanning line, when detecting the irradiation start of radiation based on leak data. It is a figure showing the procedure of each process in the radiographic imaging system which concerns on this embodiment. 6 is a diagram for explaining an example of a method for extracting preview image data from image data D. FIG. It is a figure explaining the example of the method of calculating the difference between the data for preview images. It is a figure explaining the example of the method of calculating the difference between the remaining image data. It is a figure showing distribution of the remaining image data voted for the histogram. It is a figure showing the example of the preview image etc. which were displayed on the display part of the console. It is a figure showing another structural example, such as a procedure of each process in the radiographic imaging system which concerns on this embodiment.

  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.

  Although the case where the radiographic imaging apparatus is a so-called portable type will be described, the present invention can also be applied to a so-called dedicated machine type radiographic imaging apparatus formed integrally with a support base or the like. Is possible.

[Radiation imaging equipment]
First, the configuration and the like of a radiographic image capturing apparatus used in the radiographic image capturing system according to the present embodiment will be described. FIG. 1 is a cross-sectional view of a radiographic image capturing apparatus according to the present embodiment, and FIG. 2 is a plan view illustrating a configuration of a substrate of the radiographic image capturing apparatus.

  As shown in FIG. 1, the radiographic image capturing apparatus 1 includes a scintillator 3, a substrate 4, and the like in a housing 2 formed of a carbon plate having a radiation incident surface R that is a surface irradiated with radiation. The configured sensor panel SP is housed. Although not shown in FIG. 1, in the present embodiment, the housing 2 has a wireless system that transfers image data D and the like to a console 58 (see FIGS. 4 and 5 described later) wirelessly. An antenna device 41 (see FIG. 3 to be described later) serving as communication means is provided.

  Although not shown in FIG. 1, in the present embodiment, the radiographic image capturing apparatus 1 includes a connector on the side surface of the housing 2 or the like, and a console 58 receives signals and data in a wired manner via the connector. Etc. can be transferred to. For this reason, this connector also functions as a wired communication means of the radiation image capturing apparatus 1.

  As shown in FIG. 1, a base 31 is disposed in the housing 2, and a lead thin plate or the like (not shown) is provided on the radiation incident surface R side (hereinafter simply referred to as the upper surface side) of the base 31. A substrate 4 is provided. A scintillator 3 that converts irradiated radiation into light such as visible light is provided on the scintillator substrate 34 on the upper surface side of the substrate 4, and the scintillator 3 is provided facing the substrate 4 side.

  Further, on the lower surface side of the base 31, a PCB substrate 33 on which electronic components 32 and the like are arranged, a battery 24, and the like are attached. In this way, the sensor panel SP is formed by the base 31, the substrate 4, and the like. In the present embodiment, the buffer material 35 is provided between the sensor panel SP and the side surface of the housing 2.

  In the present embodiment, the substrate 4 is formed of a glass substrate, and as shown in FIG. 2, a plurality of scanning lines 5 and a plurality of signals are provided on the upper surface 4a of the substrate 4 (that is, the surface facing the scintillator 3). The lines 6 are arranged so as to intersect each other. A radiation detection element 7 is provided in each small region r defined by the plurality of scanning lines 5 and the plurality of signal lines 6 on the surface 4 a of the substrate 4.

  In this way, the entire small region r provided with a plurality of radiation detection elements 7 arranged in a two-dimensional form (matrix) in each small region r partitioned by the scanning lines 5 and the signal lines 6, that is, FIG. The area indicated by the alternate long and short dash line in FIG. In the present embodiment, a photodiode is used as the radiation detection element 7, but a phototransistor or the like can also be used, for example.

  Here, the circuit configuration of the radiation image capturing apparatus 1 will be described. FIG. 3 is a block diagram showing an equivalent circuit of the radiation image capturing apparatus 1 according to the present embodiment.

  The first electrode 7a of each radiation detection element 7 is connected to a source electrode 8s (see “S” in FIG. 3) of the TFT 8 serving as a switching means. Further, the drain electrode 8d and the gate electrode 8g (see “D” and “G” in FIG. 3) of the TFT 8 are connected to the signal line 6 and the scanning line 5, respectively.

  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. Further, when a turn-off voltage is applied to the gate electrode 8 g via the scanning line 5, the gate electrode 8 g is turned off, the discharge of charge from the radiation detection element 7 to the signal line 6 is stopped, and charge is accumulated in the radiation detection element 7. It is supposed to let you.

  In the present embodiment, as shown in FIGS. 2 and 3, the bias line is applied to the second electrode 7 b of each radiation detection element 7 at a rate of one for each radiation detection element 7 in a row on the substrate 4. 9 is connected, and each bias line 9 is bound to the connection 10 at a position outside the detection portion P of the substrate 4.

  The connection 10 is connected to a bias power source 14 (see FIG. 3) via an input / output terminal 11 (also referred to as a pad, see FIG. 2), and the bias power source 14 connects each via the connection 10 and each bias line 9. A reverse bias voltage is applied to the second electrode 7 b of the radiation detection element 7.

  On the other hand, each scanning line 5 is connected to the gate driver 15b of the scanning driving means 15 via the input / output terminal 11, respectively. In the scanning drive means 15, an ON voltage and an OFF voltage are supplied from the power supply circuit 15a to the gate driver 15b via the wiring 15c, and applied to the lines L1 to Lx of the scanning line 5 by the gate driver 15b. The voltage is switched between an on voltage and an off voltage.

  Each signal line 6 is connected to each readout circuit 17 built in the readout IC 16 via each input / output terminal 11. In the present embodiment, the readout circuit 17 is mainly composed of an amplification circuit 18 and a correlated double sampling circuit 19. In the present embodiment, as shown in FIG. 6 described later, the amplifier circuit 18 is configured by a charge amplifier circuit in which an operational amplifier 18a and a capacitor 18b are connected in parallel, and a capacitor is connected from the output side of the operational amplifier 18a. A voltage value corresponding to the amount of charge accumulated in 18b is output.

  As shown in FIG. 3, an analog multiplexer 21 and an A / D converter 20 are further provided in the read IC 16. In FIG. 3, the correlated double sampling circuit 19 is denoted as CDS.

  In the reading process of the image data D from each radiation detection element 7, when an on-voltage is applied to the scanning line 5 from the gate driver 15b of the scanning driving means 15 and each TFT 8 is turned on, these TFTs 8 are turned on. Electric charges are emitted from the radiation detection elements 7 to the signal lines 6 through the TFTs 8. As described above, in the amplifier circuit 18 of each readout circuit 17, a voltage value corresponding to the amount of charge flowing from the radiation detection element 7 to the capacitor 18b (see FIG. 6 described later) is supplied from the operational amplifier 18a to the correlated double sampling circuit. 19 (see FIG. 3).

  The correlated double sampling circuit 19 outputs the increase in the output value from the amplification circuit 18 before and after the charge flows from each radiation detection element 7 to the amplification circuit 18 as analog value image data D on the downstream side. The output image data D is sequentially transmitted to the A / D converter 20 via the analog multiplexer 21, and is sequentially converted into digital image data D by the A / D converter 20 and stored in the storage means 23. Output and save sequentially. In this way, the reading process of the image data D is performed.

  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.

  Then, the control unit 22 controls the operation of each functional unit of the radiographic imaging apparatus 1 such as controlling the scanning driving unit 15 and the readout circuit 17 to perform the readout process of the image data D as described above. It has become.

  As shown in FIG. 3, 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 control unit 22 is connected to the antenna device 41 described above, and is further necessary for each functional unit such as the scanning drive unit 15, the readout circuit 17, the storage unit 23, and the bias power source 14. A battery 24 for supplying power is connected.

  In addition, about each process in the radiographic imaging apparatus 1 at the time of radiographic imaging, it demonstrates after describing the structure of the radiographic imaging system 50 concerning this embodiment. In the present embodiment, the control unit 22 is configured to function as a compression transfer unit of the radiographic image capturing apparatus 1 as well, which will be described later.

[Radiation imaging system]
Next, the configuration and the like of the radiation image capturing system 50 according to the present embodiment will be described. FIG. 4 is a diagram illustrating a configuration example of the radiation image capturing system 50 according to the present embodiment. In FIG. 4, the case where the radiographic imaging system 50 is constructed in the imaging room R1 is shown.

  A bucky device 51 is installed in the radiographing room R1, and the bucky device 51 can be used by loading the radiographic imaging device 1 in a cassette holding portion (also referred to as a cassette holder) 51a. It has become. FIG. 4 shows a case where a bucky device 51A for standing position shooting and a bucky device 51B for standing position shooting are installed as the bucky device 51. For example, only one of the bucky devices 51 is provided. It may be done.

  As shown in FIG. 4, at least one radiation source 52 </ b> A that irradiates 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 an access point 53 so that the radiographic imaging apparatus 1 can transmit and receive image data D, signals, and the like in a wireless manner.

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

  In the present embodiment, the front room (also referred to as an operation room) R2 is provided with an operation console 57 of the radiation generating device 55. The operation panel 57 is operated by an operator such as a radiation engineer. An exposure switch 56 is provided for instructing the generator 55 to start radiation irradiation. The radiation generating device 55 is configured to emit radiation from the radiation source 52 when the exposure switch 56 is operated by the operator. Further, various controls such as adjusting the radiation source 52 so as to emit an appropriate dose of radiation are performed.

  As shown in FIG. 4, in the present embodiment, a console 58 constituted by a computer or the like is provided in the front chamber R2. The console 58 can be configured to be provided outside the imaging room R1 and the front room R2, in a separate room, and the like, and is installed in an appropriate place.

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

  On the other hand, as shown in FIG. 5, the radiographic image capturing apparatus 1 can be used in a single state without being loaded into the bucky device 51. For example, when the patient H cannot get up from the bed B of the hospital room R3 and cannot go to the imaging room R1, the radiographic imaging device 1 is brought into the hospital room R3 as shown in FIG. It can be used by being inserted into the patient's body or applied to the patient's body.

  Further, when the radiographic image capturing apparatus 1 is used in a hospital room R3 or the like, a so-called portable radiation generating apparatus 55 is provided, for example, as a roundabout car, as shown in FIG. 5, instead of the radiation generating apparatus 55 installed in the above-described imaging room R1. It is brought into hospital room R3 by being mounted on 71 or the like.

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

  Further, in this case, a repeater 54 provided with an access point 53 is built in the radiation generator 55, and the repeater 54 communicates between the radiation generator 55 and the console 58 in the same manner as described above. The communication between the radiation image capturing apparatus 1 and the console 58, the transfer of image data D, and the like are relayed.

  As shown in FIG. 4, the radiographic imaging device 1 is composed of a body of a patient (not shown) lying down on a bucky device 51B for supine photography in the photographing room R1 and a bucky device 51B for supine photography. It can also be used by being inserted between them or being applied to the patient's body on the bucky device 51B for lying position photography. In this case, the portable radiation 52P or the radiation source 52A installed in the photographing room R1 is used. Either of these can be used.

  In the present embodiment, as will be described later, when the preview image data Dp is transferred from the radiographic image capturing apparatus 1, the console 58 generates a preview image p_pre based on the preview image data Dp and displays it on the display unit 58a. It has become.

  In this embodiment, the console 58 also functions as an image processing device. When image data D or the like is transferred from the radiographic image capturing device 1, gain correction and defective pixels are performed based on the data. The radiographic image p is generated by performing precise image processing such as correction and gradation processing according to the imaging region. These points will be described later.

[About each processing at the time of radiographic imaging in the radiographic imaging system]
Next, each process at the time of radiographic image capturing in the radiographic image capturing system 50 and the radiographic image capturing apparatus 1 according to the present embodiment will be described.

  An operator such as a radiographer operates the radiographic imaging apparatus 1 used for radiographic imaging to be performed from now on, or operates the console 58 to transmit an imaging start instruction signal from the console 58 to the radiographic imaging apparatus 1. The radiographic image capturing apparatus 1 is activated in the same manner. When the control means 22 of the radiographic image capturing apparatus 1 receives an operation input by the operator or an imaging start instruction signal from the console 58, the control unit 22 causes each functional unit to start preprocessing for radiographic image capturing. It has become.

  Specifically, necessary power is supplied from the battery 24 (see FIG. 3) to each functional unit through a power supply circuit (not shown). Then, a reverse bias voltage is applied to each radiation detection element 7 from the bias power source 14 (see FIG. 3) via the bias line 9 or the like, or the charge remaining in each radiation detection element 7 is activated by starting the scanning drive means 15. A reset process is performed for each radiation detection element 7 that releases and removes.

  The control means 22 of the radiographic image capturing apparatus 1 is configured to proceed to each process according to the radiographing method in the radiographic image capturing apparatus 1 after completing the above preprocessing. Here, an imaging method in the radiographic image capturing apparatus 1 will be briefly described.

  Radiographic imaging is roughly classified into radiographic imaging apparatus 1 and radiographic generator 55 (see FIGS. 4 and 5) that perform radiographic imaging while exchanging signals and the like (hereinafter referred to as this imaging system). And the radiation image capturing apparatus 1 and the radiation generating apparatus 55 do not exchange signals or the like, and the radiation image capturing apparatus 1 detects that radiation irradiation has started by itself. There are two photographing methods, namely, photographing methods for photographing images (hereinafter, this photographing method is referred to as a non-cooperative method).

  When radiographic imaging is performed in a cooperative manner, the control means 22 of the radiographic imaging apparatus 1 normally uses the charge remaining in each radiation detecting element 7 as the first process for radiographic imaging, with each radiation detecting element 7. It is configured to repeatedly perform reset processing of the radiation detection elements 7 emitted from the inside to the signal line 6 and the downstream side thereof.

  The same applies to the case where other methods described below are adopted. In this case, the reset processing of each radiation detection element 7 is performed from the gate driver 15b (see FIG. 3) of the scanning drive means 15 to each of the scanning lines 5. It is also possible to apply the turn-on voltage to the lines L1 to Lx in sequence, and the gate driver 15b applies the turn-on voltage to the lines L1 to Lx of the scanning line 5 all at once. It can also be configured to do so.

  In the case of the cooperation method, when an operator such as a radiation engineer operates the exposure switch 56 (see FIGS. 4 and 5) of the radiation generation apparatus 55, an irradiation start signal is transferred from the radiation generation apparatus 55 to the radiation image capturing apparatus 1. The When receiving the irradiation start signal, the control means 22 of the radiation image capturing apparatus 1 stops the reset process of each radiation detection element 7.

  At this time, the control means 22 of the radiographic image capturing apparatus 1 applies an off voltage to the lines L1 to Lx of the scanning line 5 from the gate driver 15b to turn off all the TFTs 8, and each radiation is irradiated. The charge generated in the radiation detection elements 7 is shifted to a charge accumulation state where each charge is appropriately accumulated in each radiation detection element 7. Then, an interlock release signal is transmitted to the radiation generator 55.

  Then, when receiving the interlock release signal, the radiation generating device 55 is configured to irradiate the radiation imaging apparatus 1 with radiation from the radiation source 52 (see FIG. 4 or FIG. 5) at that time. .

  On the other hand, when radiographic imaging is performed in a non-cooperative manner, as described above, the radiographic imaging apparatus 1 and the radiation generation apparatus 55 do not exchange signals or the like, so that an operator such as a radiographer can use the exposure switch 56. Even if radiation is emitted from the radiation source 52 by operating (see FIGS. 4 and 5), the information is not transmitted to the radiographic imaging apparatus 1. Therefore, it is necessary to detect that radiation irradiation has been started by the radiation image capturing apparatus 1 itself.

  Various methods can be adopted as a method of detecting the start of radiation irradiation by the radiation image capturing apparatus 1 itself. In the present embodiment, among the following methods, a method of detecting the start of radiation irradiation using leak data dleak is adopted, but the present invention is not limited to this method.

  As a method for detecting the start of radiation irradiation by the radiographic imaging apparatus 1 itself in the non-cooperative method, for example, although not shown, it is described in US Pat. No. 7,211,803, Japanese Patent Application Laid-Open No. 2009-219538, etc. As described above, it is possible to provide current detection means for detecting the value of the current flowing through the bias line 9 and the connection 10 (see FIG. 3 and the like) of the radiographic image capturing apparatus 1.

  In this case, when radiation irradiation is started on the radiation imaging apparatus 1, charges are generated in each radiation detection element 7, and the charges flow out from the radiation detection elements 7 to the bias line 9. Therefore, since the current flowing through the bias line 9 and the connection 10 increases, for example, by setting a threshold value for the detected current value, the start of radiation irradiation is detected based on the current value detected by the current detecting means. Is possible.

  Further, instead of providing such current detection means, an X-ray sensor or the like is provided in the radiation image capturing apparatus 1 so that the radiation image capturing apparatus 1 itself detects the start of radiation irradiation based on the measurement value of the X-ray sensor. It is also possible to configure.

  Further, as described above, radiographic imaging is performed using each functional unit already provided in the radiographic imaging apparatus 1 without providing the radiographic imaging apparatus 1 with new means such as current detection means and X-ray sensors. A method for detecting the start of radiation irradiation by the apparatus 1 itself has been found. For details of these detection methods, refer to International Publication No. 2011/13517 pamphlet and International Publication No. 2011/152093 pamphlet submitted by the applicants of the present application.

  Briefly described, in these detection methods, for example, the scanning drive means 15 and each readout circuit 17 (see FIG. 3) are driven before the radiation image capturing apparatus 1 is irradiated with radiation to read out image data. It is possible to repeat the process (see International Publication No. 2011-152093 pamphlet, etc.). Hereinafter, in order to distinguish from the image data D read out as the above-described main image, the image data read out before the start of radiation irradiation is hereinafter referred to as irradiation start detection data d.

  When configured in this manner, before the radiation irradiation to the radiation image capturing apparatus 1 is started, so-called dark image data that is read without radiation is read. Then, when radiation irradiation is started on the radiation image capturing apparatus 1, electric charges are generated in each radiation detection element 7 due to the radiation irradiation, and this is read as irradiation start detection data d.

  For this reason, at the time when radiation irradiation is started on the radiation imaging apparatus 1, the value of the irradiation start detection data d to be read increases rapidly. Therefore, by using the increase in the value of the irradiation start detection data d, for example, by detecting that the read irradiation start detection data d is equal to or greater than a set threshold value dth. The radiation imaging apparatus 1 itself can be configured to detect the start of radiation irradiation.

  On the other hand, as described above, instead of being configured to read out the irradiation start detection data d before the radiation imaging apparatus 1 is irradiated with radiation, each scanning line 5 is read from the gate driver 15b (see FIG. 3). It is also possible to configure each read circuit 17 to perform a read operation in a state where an off-voltage is applied to the read circuit, and to repeatedly read out the leak data dleak (see International Publication No. 2011/13517 pamphlet). .

  As shown in FIG. 6, in a state where each TFT 8 is turned off by applying an off voltage to each scanning line 5, the charge q leaked from each radiation detection element 7 through each TFT 8 in the off state. Is stored in the capacitor 18 b of the amplifier circuit 18. That is, the total value of the charge q leaked from each radiation detection element 7 via each TFT 8 is accumulated in the capacitor 18 b of the amplifier circuit 18.

  Therefore, when a read operation is performed by the read circuit 17 in this state, a voltage value corresponding to the total value of the charges q leaked from the radiation detection elements 7 via the TFTs 8 from the output side of the operational amplifier 18a of the amplifier circuit 18 is obtained. Is output. Therefore, data corresponding to the total value of the charge q leaked through each TFT 8 is read. The data read in this way is leak data dleak.

  Even in such a configuration, when radiation irradiation is started on the radiographic imaging apparatus 1, the charge q leaks from the inside of each radiation detection element 7 to the signal line 6 via each TFT 8 (see FIG. 6). Therefore, it is known that the value of the leaked data dleak to be read increases rapidly when radiation irradiation is started on the radiographic imaging apparatus 1 (see, for example, time t1 in FIG. 7).

  Therefore, by using the increase in the value of the leak data dleak, for example, as shown in FIG. 7, by detecting that the read leak data dleak is equal to or higher than a set threshold value dleak_th, The imaging device 1 itself can be configured to detect the start of radiation irradiation.

  In addition, when configured to detect the start of radiation irradiation using the leak data dleak, when the off-voltage is applied to each scanning line 5 from the gate driver 15b as described above and each TFT 8 is left in the off state, Dark charges are continuously accumulated in each radiation detection element 7.

  Therefore, for example, as shown in the left part of FIG. 8, each radiation detection element 7 is reset between the leak data dleak readout process (indicated as “L” in the figure) and the next leak data dleak readout process. The processing (described as “R” in the drawing) can be performed.

  Also in this case, when the reset processing of each radiation detection element 7 is performed, as shown in FIG. 8, the gate driver 15b (see FIG. 3) of the scanning drive unit 15 changes the lines L1 to Lx of the scanning line 5. The on-voltage may be configured to be sequentially applied, and although not shown, the on-voltage is applied to the lines L1 to Lx of the scanning line 5 from the gate driver 15b all at once. It is also possible to do.

  The radiographic imaging is performed in a different procedure in the case of the cooperative method, or the radiation irradiation start is detected by the radiographic imaging device 1 itself by a method different from the above in the case of the non-cooperative method. The present invention can also be applied to those cases.

  Also in the case of the non-cooperative method, as shown in FIG. 8, the control means 22 of the radiographic image capturing apparatus 1 detects that radiation irradiation has started on the radiographic image capturing apparatus 1 (“detection” in the figure). At that time, an off voltage is applied from the gate driver 15b to each of the lines L1 to Lx of the scanning line 5 so that all the TFTs 8 are turned off and transferred to the charge storage state.

  The control means 22 of the radiographic imaging device 1 in this way, in both the cooperative method and the non-cooperative method, after shifting to the charge accumulation state, for example, after continuing the charge accumulation state for a predetermined time, Reading processing of image data D as an image is started. In FIG. 9 to be described later, the reading process of the image data D is abbreviated as “D reading”.

  In the present embodiment, in the case of the non-cooperative system, as shown in FIG. 8, the scanning line 5 to which the on-voltage is applied in the reset process immediately before the read process of the leak data dleak that has detected the start of radiation irradiation (see FIG. 8). In the case of 8, the application of the ON voltage is started from the scanning line 5 (the line L5 of the scanning line 5 in the case of FIG. 8) to which the ON voltage is to be applied next to the line L4 of the scanning line 5). The on-voltage is sequentially applied to the scanning lines 5 to read out the image data D as the main image.

  However, the present invention is not limited to this, and the reading process of the image data D as the main image is performed by, for example, starting the application of the on-voltage from the first line L1 of the scanning line 5 as in the case of the cooperative method. It is also possible to configure such that the on-voltage is sequentially applied to each line L1 to Lx.

  On the other hand, when the control unit 22 of the radiographic image capturing apparatus 1 completes the reading process of the image data D as the main image as described above, it subsequently performs the reading process of the offset data O. In FIG. 9 to be described later, the offset data O reading process is abbreviated as “O reading”.

  In each radiation detection element 7, so-called dark charges (also referred to as dark current) are constantly generated due to thermal excitation caused by heat (temperature) of the radiation detection element 7 itself. When the reading process of the image data D as the main image is performed as described above, for example, as illustrated in FIG. 8, the voltage applied immediately before the reading process of the image data D is changed from the on voltage to the off voltage. The TFT 8 is turned off during a time Tac (hereinafter, this time Tac is referred to as an effective accumulation time Tac) from when the voltage is applied to when the voltage applied in the reading process of the image data D is switched from the on voltage to the off voltage. By being in the state, dark charges generated in each radiation detection element 7 are accumulated in each radiation detection element 7.

  The offset due to the dark charge is superimposed on the image data D read by the reading process of the main image data D. Therefore, in the offset data O reading process, the offset due to the dark charge is read as offset data O.

  Although illustration is omitted, in this embodiment, the control means 22 of the radiographic imaging device 1 repeats the same processing sequence as the processing sequence up to the reading processing of the image data D as the main image in the reading processing of the offset data O. Thus, the offset data O is read out.

  That is, when the reading process of the image data D (see FIG. 8) is completed, the control unit 22 in the cooperative method, as in the case of the radiographic imaging described above, each radiation detection element 7 before the radiographic imaging. (See “R” in FIG. 9 described later). Further, in the case of the non-cooperative method, the control means 22 ends the reading process of the image data D (see FIG. 8), the reading process of the irradiation start detection data d and the leak data dleak, and the radiation detection elements 7. A reset process is performed (see “detection” in FIG. 9 described later).

  For example, when the radiation data is captured by detecting the start of radiation irradiation using the leak data dleak as described above, the timing is the same as the timing until the reading process of the image data D shown in FIG. At the timing, the reading process (L) of the leak data dleak and the resetting process (R) of each radiation detection element 7 performed by applying the ON voltage to each of the lines L1 to Lx of the scanning line 5 are performed. In this case, it is also possible to perform the reset process of each radiation detection element 7 without performing the read process of the leak data dleak.

  Then, an off voltage is applied from the gate driver 15b to the lines L1 to Lx of the scanning line 5 to shift to the charge accumulation state. In the process of reading the offset data O, the radiation image capturing apparatus 1 is not irradiated with radiation. Then, after the charge accumulation state is continued for the same duration as the charge accumulation state before the reading process of the image data D, the ON voltage is sequentially applied to each scanning line 5 at the same timing as the reading process of the image data D. Thus, the offset data O is read out.

  With this configuration, the effective accumulation time Tac before the reading process of the image data D as the main image and the effective accumulation time Tac before the reading process of the offset data O become the same time Tac for each scanning line 5. . The dark charge is accumulated in each radiation detection element 7 by the same amount if the TFT 8 is in the off state, that is, if the effective accumulation time Tac is the same time.

For this reason, it is possible to make the offset value and the offset data O caused by the dark charge superimposed on the image data D have the same value. In the subsequent image processing in the console 58, the offset data O is subtracted from the image data D as the main image as shown in the following equation (1), thereby causing dark charges superimposed on the image data D. The offset amount and the offset data O are canceled out, and it becomes possible to calculate the true image data D ^* resulting from only the charges generated by the irradiation of radiation.
D ^* = DO (1)

[Configurations and the like unique to the present invention in a radiographic imaging system]
Next, configurations unique to the present invention in the radiographic imaging system 50 and the radiographic imaging apparatus 1 according to the present embodiment will be described. The operation of the radiographic image capturing system 50 and the radiographic image capturing apparatus 1 according to the present embodiment will also be described.

  FIG. 9 is a diagram illustrating a procedure of each process in the radiographic image capturing system 50 according to the present embodiment. Note that the time required for each process in FIG. 9 (that is, the relative length in the left-right direction of the column representing each process in FIG. 9) does not necessarily reflect reality.

  In the radiographic imaging device 1 according to the present embodiment, as described above, before radiation irradiation, the reset processing of each radiation detection element 7 (in the case of a cooperative method) and the detection process of radiation irradiation start (in the case of a non-cooperative method) ) (See “Reset detection” in the figure), and after shifting to the charge accumulation state (see “Charge accumulation” on the left side in the figure), the image data D reading process (see “D readout” in the figure) is performed. Do.

  Then, the same processing sequence is repeated again for the reading process of the offset data O, the reset process of each radiation detection element 7 and the detection process of the start of radiation irradiation are performed (see “R detection” in the figure), and the charge accumulation state (See “Charge Accumulation” on the right side in the figure), and then read the offset data O (see “O Read” in the figure).

  In this embodiment, the compression transfer unit of the radiographic image capturing apparatus 1 extracts the preview image data Dp from the read image data D at a predetermined ratio when the image data D is read. Then, the extracted preview image data Dp is compressed and transferred to the console 58 (see “Dp” in the figure).

  As described above, in the present embodiment, since the control unit 22 of the radiographic image capturing apparatus 1 is configured to function as a compression transfer unit, the following description will be given as the compression transfer unit 22. It is also possible to configure the means separately from the control means 22 of the radiation image capturing apparatus 1.

  That is, in the present embodiment, the control means 22 that is a compression transfer means, when the reading process of the image data D as the main image is finished, each radiation detection element 7 toward the reading process of the offset data O as described above. Reset processing and radiation irradiation start detection processing (see “R detection” in the figure), and at the same time, extraction of preview image data Dp from image data D and compression transfer processing are started. It is supposed to be.

  The preview image data Dp can be extracted from the read image data D as follows, for example. Here, for example, as shown in FIG. 10, the data is read from the radiation detection element 7 (n, m) in the n-th row and the m-th column of the detection unit P (see FIGS. 2 and 3) of the radiation imaging apparatus 1. Assume that the image data D is represented by D (n, m).

  The compression transfer means 22 of the radiographic image capturing apparatus 1 has a predetermined number (four in the case of FIG. 10) in advance as indicated by hatching in the drawing, for example, from the read image data D (n, m). The image data D (n, m) read out from each radiation detection element 7 connected to the scanning line 5 designated at a rate of one for each line L1 to Lx of the scanning line 5 is extracted. The preview image data is Dp.

  The method of extracting the preview image data Dp is not limited to this, and is not shown. For example, a total of 16 radiation detection elements 7 (n, m) of 4 × 4 pixels, that is, 4 rows and 4 columns, are used. The image data D is extracted from the image data D at a predetermined rate by extracting the image data D from the 16 pieces of image data D (n, m) read out from the image data D at a rate of one. The created preview image data Dp can also be configured to be extracted.

  The compression transfer means 22 compresses the extracted preview image data Dp and transmits it to the console 58. In this embodiment, at that time, the compression / transfer means 22 transfers the preview image data Dp with lossless compression, and for example, a Huffman encoding method is used as the lossless compression method. ing. In addition to the lossless compression method, other methods such as LZ78 and arithmetic coding can be used. Further, the preview image data Dp can be configured to be irreversibly compressed and transferred.

  In this embodiment, the preview dictionary data α generated in advance is used as the preview dictionary data used for the compression processing of the preview image data Dp. The dictionary data is data used as a reference when converting the original data into a compressed code. For example, when Huffman coding is used as in the present embodiment, the dictionary data is data Is generated as a table for converting to Huffman code.

  In this embodiment, as described above, the preview dictionary data used for the compression processing of the preview image data Dp is generated for each imaging for compressing the image data D necessary for generating the radiation image p described later. Unlike the image data dictionary data β, the preview dictionary data α generated in advance is used instead of being generated for each shooting.

  As described above, the reason for using the preview dictionary data α generated in advance as the preview dictionary data for compressing the preview image data Dp is as follows.

  That is, with respect to the extracted preview image data Dp, as in the case of the image data D necessary for generating the radiation image p described later, the preview dictionary data is generated for each photographing based on the preview image data Dp. According to the configuration, after the image data D is read out, preview dictionary data is generated based on the extracted preview image data Dp, and then the preview image data Dp is compressed and transferred to the console 58 based on the dictionary data. Become.

  Therefore, since it takes time to generate the dictionary data for preview, the preview image data Dp (that is, Huffman code in the case of this embodiment) compressed in the console 58 after the reading processing of the image data D is completed. ) Is transferred by the time required for generating the preview dictionary data.

  Therefore, it takes a long time to decompress the preview image data Dp compressed by the console 58 to restore the original preview image data Dp, generate a preview image p_pre based on the decompressed data Dp, and display it on the display unit 58a. Become. That is, the timing at which the preview image p_pre is displayed on the display unit 58a of the console 58 is delayed by the amount that the dictionary data for preview is newly generated by the radiation image capturing apparatus 1.

  However, in this case, an operator such as a radiologist who wants to display the preview image p_pre on the display unit 58a of the console 58 or the like as soon as possible after imaging to determine the necessity of re-imaging at an early stage. I cannot respond to the request.

  Therefore, in the present invention, as described above, the compression transfer means 22 of the radiographic image capturing apparatus 1 performs the preview image data Dp compression processing based on the preview dictionary data α generated in advance. Dp compression processing is performed.

  With such a configuration, when dictionary data is generated for each radiographing as in the compression processing of image data D necessary for generating a radiographic image p, which will be described later, the data compression rate is maximized. In such a case, In comparison, when the preview image data Dp is compressed based on the preview dictionary data α generated in advance, there is a high possibility that the compression rate will not be improved so much.

  However, if the preview image data Dp is configured to be compressed based on the preview dictionary data α generated in advance as in the present embodiment, immediately after the read processing of the image data D is completed. The preview image data Dp is extracted from the image data D read out at the same time, and the preview image data Dp is immediately generated based on the preview dictionary data α generated in advance without generating the preview dictionary data. It can be compressed and transferred to the console 58.

  Therefore, in this embodiment, the generation of preview dictionary data is generated as compared with the case where the preview dictionary data is generated as described above and then the preview image data Dp is compressed and transferred based on the preview dictionary data. The preview image data Dp that has been compressed can be transferred to the console 58 at an earlier stage after the image data D is read out as much as the time required for the processing becomes unnecessary.

  The preview image p_pre can be displayed on the display unit 58a of the console 58 as much as the preview image data Dp is transferred earlier, and the preview is displayed on the display unit 58a of the console 58 as soon as possible after shooting. It is possible to accurately respond to a request from an operator such as a radiologist who wants to display the image p_pre and determine the necessity of re-imaging at an early stage.

  In this case, the distribution of the read image data D and the distribution of the preview image data Dp extracted from the image data D may be different depending on the imaging region of the subject. That is, in the case of an overall bright image such as a hand or a leg, the ratio of the image data D having a large value increases, and for example, an overall dark image such as the front of the chest or the front of the abdomen In this case, the ratio of the image data D having a small value increases.

  Therefore, as the preview dictionary data α generated in advance, for example, a plurality of preview dictionary data α may be provided in advance in the compression transfer means 22 of the radiation image capturing apparatus 1 according to the imaging region or the like. Is possible.

  The same applies to not only the case of the preview image data Dp but also the case of compressing and transferring the image data D and offset data O necessary for generating the radiation image p, but the international application previously filed by the applicant of the present application. As described in pamphlet No. 2011/011480, Japanese Patent Application Laid-Open No. 2011-087727, etc., the extension direction of the signal line 6 or the scanning line 5 on the detection unit P (see FIGS. 2 and 3). It is also possible to calculate the difference between the data read from each radiation detection element 7 closest in the extending direction, and compress the difference and transfer the difference.

For example, when the difference between the data read from the radiation detection elements 7 closest in the extending direction of the signal line 6 is calculated, the difference ΔDp of the preview image data Dp is, for example, shown in FIG. like,
ΔDp (n + 4, m) = D (n + 4, m) −D (n, m) (2)
It is calculated as follows.

  Further, for example, the difference ΔD between the remaining image data D other than the preview image data Dp, which is image data D necessary for generating the radiation image p described later, is the extension of the signal line 6 as shown in FIG. The difference between the image data D adjacent in the direction is calculated. If the adjacent image data D is the preview image data Dp, the difference is calculated by skipping the difference.

  Thus, when the differences ΔDp, ΔD, ΔO between the preview image data Dp, the remaining image data D, or the offset data O (not shown) are calculated, the distribution of the differences ΔDp, ΔD, ΔO is as follows: In both cases, the distribution is a normal distribution centered on ± 0. Even in the case where the imaging region of the subject is different, in most cases, the difference in the data is a distribution with a normal distribution centered on ± 0.

  Therefore, preview dictionary data based on such a normal distribution centered around ΔDp = 0 is used as preview dictionary data α generated in advance at least when the difference ΔDp of the preview image data Dp is compressed. If only α is generated in advance, the difference ΔDp in the preview image data Dp is compressed based on one preview dictionary data α generated in advance even if the imaging region of the subject changes with each imaging. It becomes possible to compress appropriately with a relatively high rate.

  Therefore, by configuring the data difference to be compressed in this way, at least in the compression process of the preview image data Dp, it is generated in advance as compared with the case where the preview image data Dp itself is compressed as described above. There is no need to provide a plurality of preview dictionary data α, and it is possible to compress the difference ΔDp with a sufficiently high compression rate with a single preview dictionary data α generated in advance.

  As described above, the compression transfer unit 22 of the radiographic image capturing apparatus 1 extracts the preview image data Dp from the read image data D as described above when the read processing of the image data D is performed. Then, the extracted preview image data Dp (or the difference ΔDp, hereinafter the same) is compressed and transferred to the console 58 (see “Dp” in FIG. 9).

  Since the preview dictionary data α for compressing the preview image data Dp is generated in advance as described above, the preview generated by the radiographic imaging apparatus 1 in the console 58 is also generated in the console 58. It is possible to have the same preview dictionary data α as the dictionary data α. Therefore, in the present embodiment, the console 58 is configured to include the same preview dictionary data α as the preview dictionary data α generated in advance in the radiation image capturing apparatus 1.

  Further, as described above, when the radiation image capturing apparatus 1 side is configured to include a plurality of types of preview dictionary data α generated in advance according to the imaging region of the subject, radiation is also generated on the console 58 side. A plurality of types of preview dictionary data α that are the same as the previously generated preview dictionary data α of the image capturing apparatus 1 are provided.

  Then, the information of the preview dictionary data α used for the console 58 is transmitted from the radiographic image capturing apparatus 1 or the preview dictionary data α used for the radiographing to the radiographic image capturing apparatus 1 from the console 58 side. , And on the console 58 side, the preview image data Dp compressed by using the same preview dictionary data α as the preview dictionary data α used by the radiographic imaging device 1 for the compression processing of the preview image data Dp. Can be configured to extend.

  On the other hand, in this embodiment, as shown in FIG. 9, the compression transfer means 22 of the radiographic image capturing apparatus 1 uses image data for compressing image data D necessary for generating the radiographic image p in parallel therewith. Dictionary data β is generated (see “β” in FIG. 9). The compression transfer means 22 compresses the image data D necessary for generating the radiation image p based on the generated image data dictionary data β and transfers the compressed image data D to the console 58.

  In the present embodiment, as the image data D necessary for generating the radiation image p at the console 58, the remaining image data D other than the preview image data Dp (see image data D not hatched in FIG. 10). ) Are compressed and transferred to the console 58.

  In the present embodiment, the compression transfer unit 22 of the radiographic image capturing apparatus 1 compresses the remaining image data D, which is the image data D necessary for generating the radiographic image p, in order to compress the remaining image data. Based on D, image data dictionary data β is generated for each radiographic image capture. In the following, the case of such a configuration will be described, but other configuration examples will be described later.

  That is, in the present embodiment, the compression transfer unit 22 of the radiographic image capturing apparatus 1 does not use the dictionary data generated in advance as in the case of the preview image data Dp for the remaining image data D, but captures each radiographic image. In addition, based on the remaining image data D, image data dictionary data β for compressing the remaining image data D is generated.

  In this embodiment, as shown in FIG. 9, the image data dictionary data β generation process (see “β” in the figure) is performed while the preview image data Dp is extracted and transferred. To do.

  That is, the actual compression / transfer processing of the remaining image data D is performed after the offset data O reading processing, and the image data dictionary data β used for the compression / transfer processing of the remaining image data D at that time is the image data It is generated at the time of compression transfer processing of preview image data Dp after data D is read.

  If the generation of the image data dictionary data β is performed, for example, after the reading process of the offset data O, the start of the compression transfer process of the remaining image data D is delayed while waiting for the generation of the image data dictionary data β. There is a possibility.

  However, as described above, the image data dictionary data β is generated in advance after the reading process of the image data D, so that, as will be described later, immediately after the reading process of the offset data O, the remaining image data D is immediately stored. It becomes possible to start compression transfer processing and the like. In addition, the cycle time Tc from when the image is taken until the next image can be taken can be shortened accordingly.

  In addition, although illustration is abbreviate | omitted, the read-out process of offset data O may be comprised so that it may perform before radiation irradiation with respect to the radiographic imaging apparatus 1. In such a case, when the reading process of the image data D is completed, the compression / transfer process of the remaining image data D must be performed immediately after the compression / transfer process of the preview image data Dp.

  However, even in such a case, as described above, the remaining image data D based on the remaining image data D in parallel with the compression transfer processing of the preview image data Dp (see “Dp” in FIG. 9). If the processing for generating the image data dictionary data β corresponding to is performed, the generation processing of the image data dictionary data β is completed by the end of the compression and transfer processing of the preview image data Dp. After the preview image data Dp is compressed and transferred, the remaining image data D can be immediately compressed and transferred.

  Therefore, in this case as well, the remaining image data D can be compressed and transferred to the console 58 without delay. Therefore, until the next shooting can be performed after shooting for that amount. It is possible to obtain an effect that the cycle time Tc can be shortened.

  In the present embodiment, the following generation method is adopted as a method of generating the image data dictionary data β.

That is, the remaining image data D other than the preview image data Dp among all the image data D is voted on the histogram H whose class is each image data D (or each difference ΔD between the image data D; the same applies hereinafter). To do. If the image data D can take a value of 0 to 65535 (= 2 ¹⁶ −1), for example, the remaining images in the histogram H having 0 to 1, 1 to 2,..., 65534 to 65535 as the respective classes. Vote for data D.

  If the distribution when all the remaining image data D has been voted is a distribution as shown in FIG. 13, for example, in this embodiment, the compression transfer means 22 of the radiographic image capturing apparatus 1 uses the frequency F. The image data dictionary data β is generated by assigning shorter codes (in this embodiment, Huffman codes; the same applies hereinafter) in order from the highest class.

  When the image data dictionary data β is generated in this way, the distribution of the frequency F of the remaining image data D may be different for each shooting, but based on the actual distribution of the remaining image data D that is different for each shooting. Thus, a short code is assigned to the remaining image data D having a high frequency F, that is, an appearance frequency, and a longer code is assigned to the remaining image data D having a low frequency F, that is, an appearance frequency.

  Therefore, the image data dictionary data β is accurately matched to the actual distribution of the remaining image data D, and the remaining image data D can be compressed in a state where the compression rate is maximized. Dictionary data can be used.

  Therefore, by compressing the remaining image data D using such image data dictionary data β and transferring it to the console 58, the amount of data to be transferred, that is, the data amount of the remaining compressed image data D The time required for transfer can be further shortened. Therefore, it is possible to obtain an effect that the cycle time Tc from the time when the image is taken to the time when the next image can be taken can be shortened.

  As described above, instead of compressing and transferring the remaining image data D itself, a difference ΔD between the remaining image data D (the same applies to a difference ΔO between offset data O described later). In some cases, the calculated difference ΔD may be compressed and transferred. In this case, instead of the image data dictionary data β, the difference dictionary data β is generated based on the distribution of the difference ΔD, and the same processing as described above is performed.

  On the other hand, in the present embodiment, as described above, the compression transfer unit 22 of the radiographic image capturing apparatus 1 performs the remaining image data D after completion of the offset data O reading process (see “O reading” in FIG. 9). Is compressed and transferred (see “Remaining D” in FIG. 9). At this time, as described above, the image data dictionary data β is generated for each radiographing. Therefore, before transferring the remaining image data D, the image data dictionary data β is transferred from the radiation image radiographing apparatus 1 to the console. 58 (see “β, remaining D” in FIG. 9).

  In the present embodiment, the compression transfer unit 22 also compresses and transfers the offset data O. The compression transfer means 22 generates the offset data dictionary data γ corresponding to the offset data O based on the read offset data O for the offset data O (in FIG. 9). (See “γ”).

  In this embodiment, as shown in FIG. 9, after the offset data O reading process is completed, the transfer process of the image data dictionary data β to the console 58 and the remaining data based on the image data dictionary data β are performed. The image data D is compressed and transferred, and at the same time, the offset data dictionary data γ is generated.

  For example, the offset data dictionary data γ can be generated by voting the offset data O on a histogram (see FIG. 13) in the same manner as described above.

  With this configuration, the offset data dictionary data γ can be generated while the image data dictionary data β is transferred and the remaining image data D is compressed and transferred. Therefore, as soon as the transfer of the image data dictionary data β and the remaining image data D is completed, the compression transfer process of the offset data O based on the offset data dictionary data γ can be started.

  Therefore, it is possible to transfer the offset data dictionary data γ and the compressed offset data O to the console 58 without delay, and accordingly, a cycle from the time when shooting is performed until the next shooting can be performed. There is an effect that the time Tc can be shortened.

[Console processing]
On the other hand, in the console 58, as described above, the preview image data Dp compressed from the radiographic image capturing apparatus 1 after the reading process of the image data D in the radiographic image capturing apparatus 1 (Huffman code in the present embodiment; the same applies hereinafter). Is transferred, the compressed preview image data Dp is expanded by using the same dictionary data α as the previously generated dictionary data α of the radiographic image capturing apparatus 1 to obtain the original preview image data Dp. Restore.

  The same applies to the remaining image data D, offset data O, and the like. However, in the case where the difference ΔDp of the preview image data Dp is compressed and transferred, the console 58 displays the radiation image. Using the same dictionary data α as the dictionary data α generated in advance by the imaging apparatus 1 (in the case of the remaining image data D and offset data O, the image data dictionary data β transferred from the radiographic imaging apparatus 1 or Using the offset data dictionary data γ), the transferred difference ΔDp is expanded to restore the original difference ΔDp. Then, the original preview image data Dp is restored based on the restored original difference ΔDp.

  Then, the console 58 generates a preview image p_pre based on the restored preview image data Dp, and wipes and displays the preview image p_pre on the display unit 58a as shown in FIG. 14, for example. Then, the console 58 displays an “OK” button icon 60a and an “NG” button icon 60b below the preview image p_pre, for example.

  An operator such as a radiologist looks at the displayed preview image p_pre, determines whether or not the subject is appropriately captured in the image, and determines whether re-imaging is necessary. If there is no need to re-shoot, the “OK” button icon 60a is clicked. Instead of being configured to click the “OK” button icon 60a, for example, when the “NG” button icon 60b is not clicked within a predetermined time after the preview image p_pre is displayed, there is no need to re-shoot. It can also be configured to be determined.

  If the operator who has viewed the displayed preview image p_pre determines that re-shooting is necessary, the user clicks the “NG” button icon 60b. In this case, in order to immediately make the radiographic imaging device 1 ready for reimaging, the radiographic imaging device 1 is configured to transmit a stop signal from the console 58 to the radiographic imaging device 1, for example. Upon reception, processing such as offset data O readout processing that is being performed at that time is stopped, reset processing (in the case of a cooperative method) of each radiation detection element 7 and detection processing of radiation irradiation start for re-imaging. It is also possible to configure to resume (in the case of a non-cooperation method).

  Further, when the image data dictionary data β and the remaining compressed image data D are transferred from the radiographic imaging apparatus 1, the console 58 is compressed based on the transferred image data dictionary data β. The remaining image data D is decompressed to restore the original remaining image data D. Then, the restored original remaining image data D and the already restored preview image data Dp are combined, that is, the preview image data Dp extraction processing from the entire image data D shown in FIG. The reverse process is performed to restore all original image data D.

  Further, when the console 58 receives the offset data dictionary data γ and the compressed offset data O from the radiographic imaging apparatus 1, the console 58 compresses the offset based on the transferred offset data dictionary data γ. The original offset data O is restored by decompressing the data O.

Then, according to the above equation (1), for each radiation detection element 7 of the radiation image capturing apparatus 1, the offset data O restored from the restored image data D is subtracted to calculate the true image data D ^* , The true image data D ^* for each radiation detection element 7 is subjected to precise image processing such as gain correction, defective pixel correction, gradation processing according to the imaging region, and the like, and the radiation image p is generated. Yes. The generation process of the radiation image p is a well-known process, and the description thereof is omitted.

  When the console 58 generates the radiation image p in this way, in this embodiment, the console 58 displays the radiation image p on the display unit 58a so as to overwrite the preview image p_pre shown in FIG. Similarly to the preview image p_pre illustrated in FIG. 14, for example, an “OK” button icon 60 a and an “NG” button icon 60 b are displayed below the radiation image p.

  Then, an operator such as a radiographer performs image quality adjustment or the like of the generated radiographic image p as necessary, and then clicks an “OK” button icon 60a to approve the radiographic image p. Then, when the radiographic image p is approved in this way, the console 58 determines the radiographic image p.

  In this embodiment, when the radiographic image p is approved, the console 58 transmits a signal to the radiographic image capturing apparatus 1. When the radiographic image capturing apparatus 1 receives this signal, A state in which a reset process (in the case of the cooperative method) of each radiation detection element 7 and a detection process of the start of irradiation of radiation (in the case of the non-cooperative method) are started for the next photographing. It is supposed to be moved to.

  That is, in this embodiment, as shown in FIG. 9, an operator such as a radiologist operates the exposure switch 56 (see FIGS. 4 and 5) to irradiate the radiation imaging apparatus 1 with radiation and perform imaging. The time interval from when the radiographic image p is generated to the radiographic image p generated by the console 58 based on the data obtained by the imaging until the radiographic image p is determined is the cycle time Tc.

  Then, by configuring as described above, the image data dictionary data β is voted for each image, and the remaining image data D is voted on the histogram H (see FIG. 13), and the frequency F is shortened in descending order. The compression rate is increased to the highest level by generating the code by allocating the code so as to accurately match the distribution of the actual frequency F of the remaining image data D. So that it can be compressed.

  Therefore, the data amount of the remaining compressed image data D can be further reduced, and the time required for transfer can be further shortened. Therefore, the cycle time Tc (see FIG. 9) from when the image is taken until the next image can be taken can be accurately shortened accordingly.

  Also, as shown in FIG. 9, the image data dictionary data β is generated while the preview image data Dp is extracted and transferred, and the offset data dictionary is also used for the offset data O for each photographing. By configuring so as to generate the data γ, it is possible to further shorten the cycle time Tc from when the image is taken until the next image can be taken.

  In the case of the remaining image data D, for example, the distribution of the remaining image data D on the histogram H is different if the imaging region is different for each radiographic imaging, so the image data is different for each imaging. The dictionary data β is generated and applied to the remaining image data D, so that the remaining image data is most suitable for the remaining image data D whose distribution changes with every shooting and the compression rate is maximized. Image data dictionary data β capable of compressing D is obtained.

  However, since the offset data O is data due to dark charges generated by the heat (temperature) of the radiation detection element 7 as described above, the offset data O is read unlike the case of the remaining image data D described above. The offset data O is a value that does not depend on the imaging region or the like, and is almost the same for each radiographic image capture. Although illustration is omitted, the distribution of the offset data O obtained by voting the offset data O to the histogram also becomes a distribution that hardly changes with each photographing.

  Therefore, in the case of the offset data O, unlike the case of the remaining image data D described above, the dictionary data for offset data O created in advance is not generated for each photographing, but the dictionary data for offset data O is generated. Even when the offset data O is compressed by using, the compression rate hardly decreases.

  Therefore, for the offset data O, instead of generating and applying the offset data dictionary data γ for each shooting as in the present embodiment, compression processing is performed using dictionary data for offset data O created in advance. It is also possible to configure as described above. Even with this configuration, the offset data O can be appropriately compressed and transferred to the console 58 in a short time, so that the next shooting can be performed after shooting. It is possible to further shorten the cycle time Tc.

[effect]
As described above, according to the radiographic image capturing system 50 and the radiographic image capturing apparatus 1 according to the present embodiment, the compression transfer unit 22 of the radiographic image capturing apparatus 1 is, for example, other than the preview image data Dp for each radiographic image capturing. The distribution of the actual frequency F of the image data D necessary for generating the radiographic image p with respect to the image data D necessary for generating the radiographic image p, such as the remaining image data D, is accurately determined (see, for example, FIG. 13). The image data dictionary data β is generated by matching.

  Further, the console 58 decompresses the image data D necessary for generating the radiation image p based on the image data dictionary data β transferred from the radiation image capturing apparatus 1, and restores the original image data D, thereby restoring the image data D. The radiation image p is generated based on the original image data D.

  Therefore, by configuring in this way, it is possible to compress the image data D necessary for generating the radiation image p in a state where the compression rate is maximized. Therefore, the data amount of the compressed image data D can be further reduced, and the time required for transferring the compressed image data D can be further shortened. Therefore, the cycle time Tc (see FIG. 9) from when the image is taken until the next image can be taken can be accurately shortened accordingly.

  Therefore, it becomes possible to respond to the request of an operator such as a radiologist who wants the cycle time Tc to be as short as possible, for example, when radiographic imaging must be performed one after another, such as chest X-ray imaging in a mass examination. In addition, an operator such as a radiographer can perform imaging one after another in a short time. Therefore, the radiographic image capturing system 50 and the radiographic image capturing apparatus 1 are convenient for the operator.

  On the other hand, according to the radiographic image capturing system 50 and the radiographic image capturing apparatus 1 according to the present embodiment, the compression transfer unit 22 of the radiographic image capturing apparatus 1 compresses and transfers the preview image data Dp as described above. Instead of generating the preview dictionary data for each shooting, the preview image data Dp is compressed based on the preview dictionary data α generated in advance and transferred to the console 58.

  Further, the console 58 includes preview dictionary data α that is the same as the preview dictionary data α generated in advance by the radiographic image capturing apparatus 1, and the preview image data Dp compressed from the radiographic image capturing apparatus 1 is transferred. Then, the preview image data Dp compressed based on the preview dictionary data α provided in advance is decompressed to restore the original preview image data Dp, and the preview image p_pre is generated based on the decompressed preview image data Dp. Are displayed on the display unit 58a.

  And if comprised in this way, after completion | finish of the read-out process of the image data D in the radiographic imaging device 1, without generating the preview dictionary data (alpha) again, the preview image data Dp will be immediately created from the image data D. The extracted data can be compressed based on the preview dictionary data α and transferred to the console 58.

  Therefore, compared to the case where the preview dictionary data is generated and then the preview image data Dp is compressed and transferred based on the preview dictionary data, the time required for generating the preview dictionary data is unnecessary. Only after the image data D is read out, the preview image data Dp compressed to the console 58 can be transferred earlier.

  The preview image p_pre can be displayed on the display unit 58a of the console 58 as much as the preview image data Dp is transferred earlier, and the preview is displayed on the display unit 58a of the console 58 as soon as possible after shooting. It is possible to accurately respond to a request from an operator such as a radiologist who wants to display the image p_pre and determine the necessity of re-imaging at an early stage.

  In the present embodiment, the preview image data Dp is transferred from the radiographic image capturing apparatus 1 to the console 58 after the preview image data Dp is transferred. The case where the remaining image data D other than Dp is compressed and transferred has been described.

  However, depending on the radiation image capturing system 50, after the preview image data Dp is transferred, all the image data D including the preview image data Dp is compressed and transferred from the radiation image capturing apparatus 1 to the console 58. Sometimes it is.

  In such a case, instead of generating the image data dictionary data β for compressing the remaining image data D other than the preview image data Dp for each radiographic image capture as in this embodiment, for example, The image data dictionary data β can be generated for all the image data D by voting all the read image data D to the histogram H (see FIG. 13). It is.

  With this configuration, as in the case of the above-described embodiment, all the image data D is compressed in a state where the compression rate is maximized based on the data distribution for all the image data D. Thus, the time required for transferring the image data D can be greatly reduced. Therefore, it is possible to obtain the same beneficial effect as in the case of the present embodiment.

  On the other hand, even if it is configured to transfer the remaining image data D as the image data D necessary for generating the radiation image p as in the present embodiment, it is compressed as described above. The image data dictionary data β may be generated based on all the image data D including the preview image data Dp.

  That is, in this case, not the remaining image data D but all the image data D are voted on the histogram H (see FIG. 13), and image data dictionary data β is generated based on the distribution. Even with this configuration, the distribution on the histogram H is almost the same as when only the remaining image data D is voted, and image data dictionary data β almost the same as that is generated.

  Therefore, even when configured as described above, it is possible to compress the remaining image data D with the compression rate close to the maximum degree based on the generated image data dictionary data β. The same beneficial effect can be obtained.

  Further, as described above, the difference ΔD between the remaining image data D, not the remaining image data D itself, is calculated, and the difference dictionary data β is generated based on the difference ΔD. It is also possible to construct the dictionary data β so that the difference between the image data D is calculated for all the image data D and not based on the difference ΔD between the remaining image data D and generated based on them. .

  Even with this configuration, it is possible to compress the difference ΔD between the remaining image data D based on the generated difference dictionary data β in a state where the compression rate is close to the maximum. Then, it is possible to obtain the same beneficial effect as in the case where the difference dictionary data β is generated based on the difference ΔD between the remaining image data D.

  On the other hand, the time required for the transfer processing of the image data dictionary data β and the offset data dictionary data γ is usually much shorter than the time required for the compression transfer processing of the remaining image data D and offset data O. That's it.

  Therefore, as described above, the image data dictionary data β and the like are generated in accordance with the distribution of the actual frequency F of the remaining image data D and the like as described above, and the remaining image data D and the like are compressed based on it. If it is configured to compress and transfer in a state where the rate is maximized, the contribution of shortening the transfer time of the remaining image data D and the like becomes very large.

  Therefore, if the remaining image data D is compressed and transferred in a state where the compression rate is maximized as described above, the image data dictionary data β and the like are transferred together with it. Even after all, it is possible to sufficiently shorten the time required for transferring the image data dictionary data β and the like and the remaining compressed image data D and the like. Therefore, the cycle time Tc can be accurately shortened.

  In the above embodiment, as shown in FIG. 9, after the offset data O reading process (see “O reading” in the figure) is completed, the generation of the offset data dictionary data γ is started at the same time. Transfer processing of generated image data dictionary data β (see “β”), compression transfer processing of remaining image data D based on image data dictionary data β (see “Remaining D”), dictionary data for offset data The case where the transfer process of γ (see “γ”) and the compression transfer process of offset data O based on the dictionary data for offset data γ (see “O”) have been described.

  In this case, as described above, the processing in the console 58 includes the preview image data Dp that has already been transferred and restored after the reading processing of the image data D in the radiation image capturing apparatus 1 and the offset of the radiation image capturing apparatus 1. The remaining image data D transferred and restored after the data O reading process is synthesized, and the entire image data D is temporarily restored. Then, the order is such that the radiation image p is generated based on all the restored image data D and the offset data O transferred and restored after the offset data O reading process.

  Therefore, after the preview image p_pre is wiped displayed on the display unit 58a of the console 58 as shown in FIG. When the console 58 generates the radiation image p and displays the generated radiation image p so as to overwrite the preview image p_pre, the display on the display unit 58a is switched from the preview image p_pre to the radiation image p. It becomes like this.

  There is no problem with this configuration, but while the preview image p_pre continues to be displayed on the display unit 58a, an operator such as a radiologist can see how much the processing at the console 58 is progressing. I can't know. Therefore, for example, by configuring as follows, it is possible to inform the operator how much the processing in the console 58 is progressing.

  That is, as illustrated in FIG. 9, after the reading process of the offset data O in the radiographic image capturing apparatus 1, instead of performing the image data dictionary data β in order to the compression transfer process of the offset data O in order, For example, as shown in FIG. 15, after the offset data O reading process, 1/4 offset data corresponding to the preview image data Dp that has already been transferred (see image data D shown by hatching in FIG. 10). O is transferred, the image data dictionary data β and the remaining compressed image data D are transferred, and then the offset data dictionary data γ and the remaining compressed 3/4 offset data O are transferred. Is possible.

  The above-mentioned “1/4” and “3/4” are values corresponding to the case where the preview image data Dp is extracted from the image data D at a ratio of 1/4 as shown in FIG. When extracted at other ratios, these values correspond to the ratios.

  In the above case, the 1/4 offset data O is generated in advance because it is not the generated dictionary data for offset data γ, but is compressed and transferred quickly without waiting for the generation of dictionary data as described above. It is compressed and transferred using the dictionary data for offset data.

  Further, in this case, when the offset data dictionary data γ is generated for each photographing, the offset data dictionary data γ is generated based on the remaining 3/4 offset data O to be compressed and transferred later. Alternatively, the entire offset data O may be generated as a target. Also in this case, the remaining 3/4 offset data O may be compressed using dictionary data for offset data O created in advance.

  In the console 58, when the 1/4 offset data O compressed from the radiographic imaging device 1 is transferred, the console 58 compresses the data based on the same dictionary data as the dictionary data generated in advance by the radiographic imaging device 1. The 1/4 offset data O is expanded to restore the original 1/4 offset data O.

Then, according to the above equation (1), the corresponding restored offset data O is subtracted from the already restored preview image Dp (corresponding to the image data D of the above equation (1)), and each radiation detection of the radiographic image capturing apparatus 1 is detected. True image data D ^* is calculated for each element 7. Although only about 1/4 of the entire data, at this point in time, the calculated true image data D ^{* is} subjected to precise correction such as gain correction, defective pixel correction, and gradation processing according to the imaging region. Image processing is performed to generate a temporary radiation image p. Then, the generated temporary radiation image p is displayed so as to be overwritten on the preview image p_pre displayed on the display unit 58a.

  With this configuration, when the display on the display unit 58a is switched from the preview image p_pre to the temporary radiation image p, an operator such as a radiologist recognizes that the processing in the console 58 has progressed to that stage. It becomes possible to do.

After that, when the remaining compressed image data D and the remaining compressed ¾ offset data O are transferred, the console 58 decompresses them and restores the original remaining image data D and the remaining data. 3/4 of the offset data O is restored, and true image data D ^* is calculated therefrom.

Then, these true image data D ^*, and all the true image data by synthesizing the true image data D ^* corresponding to the preview image data Dp calculated above D ^*. Then, precise image processing such as gain correction, defective pixel correction, and gradation processing corresponding to the imaging region is performed on all the calculated true image data D ^* to generate a final radiation image p, The temporary radiation image p displayed on the display unit 58a is displayed so as to be overwritten.

  In this way, the final radiographic image p is overwritten and displayed on the temporary radiographic image p, so that an operator such as a radiographer can confirm that the generation process of the radiographic image p in the console 58 has been completed. It becomes possible to recognize. In this way, by configuring as described above, it becomes possible for an operator such as a radiographer to accurately recognize how much the processing in the console 58 is progressing, and the radiographic imaging system 50 There is an effect that it is convenient for the operator.

  Needless to say, the present invention is not limited to the above-described embodiments and modifications, and can be appropriately changed without departing from the gist of the present invention.

DESCRIPTION OF SYMBOLS 1 Radiation imaging device 5 Scan line 6 Signal line 7 Radiation detection element 8 TFT (switch means)
15 Scanning drive means 17 Reading circuit 22 Control means (compression transfer means)
41 Antenna device (communication means)
50 Radiation image capturing system 58 Console 58a Display unit D Image data Dp Preview image data F Frequency H Histogram O Offset data p Radiation image p_pre Preview image q Charge α Preliminarily generated preview dictionary data β Image data dictionary data (difference Dictionary data)
γ Offset data dictionary data (difference dictionary data)
ΔD, ΔDp, ΔO Difference

Claims (11)

A plurality of scanning lines and a plurality of signal lines arranged to cross each other;
A plurality of radiation detection elements arranged two-dimensionally;
Scanning drive means for switching a voltage applied to each scanning line between an on-voltage and an off-voltage,
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 for reading out the electric charge emitted from the radiation detection element as image data;
Control means for controlling at least the scanning drive means and the readout circuit to read out the image data from each of the radiation detection elements;
A communication means capable of communicating with the console;
Compression transfer means for compressing and transferring data obtained by radiographic imaging to the console via the communication means;
A radiographic imaging device comprising:
The console including a display unit;
With
The compression transfer unit of the radiographic image capturing apparatus includes:
Preview image data is extracted from the read image data at a predetermined ratio, and the extracted preview image data is compressed based on preview dictionary data generated in advance and transferred to the console. With
Necessary for generating image data dictionary data for compressing the image data necessary for generating a radiographic image for each radiographic image capturing, transferring the image data dictionary data to the console, and generating the radiographic image Image data is compressed based on the image data dictionary data and transferred to the console,
The console is
When the preview image data is transferred from the radiographic image capturing apparatus, the preview dictionary data is the same as the previously generated preview dictionary data included in the radiographic image capturing apparatus. Decompressing the compressed preview image data based on the dictionary data for restoring the original preview image data, generating a preview image based on the decompressed preview image data, and displaying it on the display unit;
When the image data dictionary data and the image data necessary for generating the compressed radiation image are transferred from the radiation image capturing apparatus, the radiation image of the radiation image is transferred based on the transferred image data dictionary data. A radiographic imaging system characterized in that image data necessary for generation is expanded to restore original image data, and a radiographic image is generated based on all the restored original image data.   The compression transfer means of the radiographic imaging apparatus votes the image data necessary for generating the radiographic image in a histogram, and assigns shorter codes in order from the highest frequency class to the image data dictionary. The radiographic imaging system according to claim 1, wherein data is generated. The compression transfer unit of the radiographic image capturing apparatus generates the image data dictionary data based on the remaining image data other than the preview image data in the image data, and the generated image data dictionary data Is transferred to the console, and the remaining image data is compressed based on the image data dictionary data and transferred to the console,
The console restores the remaining image data compressed based on the transferred image data dictionary data, and performs radiation based on the restored remaining image data and the restored preview image data. The radiation image capturing system according to claim 1, wherein an image is generated. The compression transfer means of the radiographic image capturing apparatus generates the image data dictionary data based on all the image data, transfers the generated image data dictionary data to the console, and among the image data The remaining image data other than the preview image data is compressed based on the image data dictionary data and transferred to the console,
The console restores the remaining image data compressed based on the transferred image data dictionary data, and performs radiation based on the restored remaining image data and the restored preview image data. The radiation image capturing system according to claim 1, wherein an image is generated. The compression transfer means of the radiographic image capturing apparatus generates the image data dictionary data based on all the image data, transfers the generated image data dictionary data to the console, and all the image data Is compressed based on the image data dictionary data and transferred to the console,
The console restores all the image data compressed based on the transferred dictionary data for image data, and generates a radiation image based on all the restored image data. The radiographic imaging system of Claim 1 or Claim 2.   The compression transfer unit of the radiographic imaging apparatus performs the generation process of the image data dictionary data while the extraction process and transfer process of the preview image data are being performed. The radiographic imaging system as described in any one of Claims 5-6. The control unit of the radiographic imaging apparatus, after the reading process of the image data, controls at least the scanning driving unit and the reading circuit, and reads an offset amount superimposed on the image data as offset data Let the data read process,
The compression transfer unit of the radiographic image capturing apparatus generates offset data dictionary data for compressing the offset data based on the read offset data, and transfers the offset data dictionary data to the console. The radiographic imaging system according to any one of claims 1 to 6, wherein the offset data is compressed based on the offset data dictionary data and transferred to the console. The control unit of the radiographic imaging apparatus, after the reading process of the image data, controls at least the scanning driving unit and the reading circuit, and reads an offset amount superimposed on the image data as offset data Let the data read process,
The compression transfer unit of the radiographic image capturing apparatus compresses the read offset data based on dictionary data for offset data created in advance and transfers the compressed data to the console. Item 7. The radiographic image capturing system according to any one of Items 6. The compression transfer unit of the radiographic image capturing apparatus includes:
After the image data read processing, the preview image data is compressed and transferred to the console,
8. The offset data corresponding to the preview image data, the remaining image data, and the remaining offset data are transferred to the console in this order after the offset data read processing, respectively. Item 9. The radiographic image capturing system according to Item 8. The compression transfer unit of the radiographic image capturing apparatus includes:
Instead of compressing and transferring the preview image data and the image data necessary for generating the radiation image to the console, the difference between the preview image data between the predetermined radiation detection elements and the generation of the radiation image Calculate the difference of image data necessary for
The difference between the preview image data is compressed based on dictionary data generated in advance and transferred to the console,
For the difference between the image data necessary for generating the radiographic image, difference dictionary data for compressing the difference is generated based on the calculated difference, and the difference dictionary data is transferred to the console. In addition, the difference is compressed based on the difference dictionary data and transferred to the console,
The console is
The dictionary data is the same as the previously generated dictionary data included in the radiographic image capturing device, and when the compressed difference between the preview image data is transferred from the radiographic image capturing device, the dictionary The compressed difference is expanded based on the data to restore the original difference, the original preview image data is restored based on the restored original difference, and a preview image is generated based on the original preview image data. As well as
When the compressed difference between the dictionary data for difference and the image data necessary for generating the radiation image is transferred from the radiographic imaging device, the compression is performed based on the transferred dictionary data for difference. The original difference is restored by decompressing the restored difference, the image data necessary for generating the original radiation image is restored based on the restored original difference, and the radiation image is obtained based on the restored original whole image data The radiographic imaging system according to claim 1, wherein:   A radiographic image capturing apparatus, which is used in the radiographic image capturing system according to claim 1.

Images