JP5626225B2 - Radiographic imaging apparatus and radiographic imaging system - Google Patents

Description

  The present invention relates to a radiographic image capturing apparatus and a radiographic image capturing system, and more particularly to a radiographic image capturing apparatus and a radiographic image capturing system capable of continuous image capturing and long image capturing.

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

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

  In addition, unlike conventional screen film and CR (Computed Radiography) devices that do not allow over-shooting, there is no need to change the film or photostimulable phosphor sheet for each radiographic image. Alternatively, it is configured such that image data for every several tens of images can be stored in a storage means such as a DRAM (Dynamic RAM) built in the apparatus.

  Therefore, using a radiographic imaging device, for example, so-called continuous imaging in which a subject (that is, a subject) continuously irradiates radiation while gradually changing the direction of the subject (ie, a subject) with respect to the radiographic imaging device, or a radiographic image of a subject For example, it is possible to perform so-called long photographing in which a wide range of the subject's body is photographed while changing the position of the photographing apparatus (see, for example, Patent Document 4).

  By the way, at the time of radiographic imaging, when radiation is irradiated to such a radiographic imaging device through a subject, an electromagnetic wave converted from the radiation by a radiation detecting element irradiated with the radiation, a scintillator or the like is incident. A charge is generated in the radiation detection element according to the dose of the irradiated radiation, and after imaging, this charge is read out and detected as image data for each radiation detection element.

  Also, in each radiation detection element, so-called dark charges are constantly generated due to thermal excitation of each radiation detection element itself by heat, etc., and at the time of image reading processing for reading image data from each radiation detection element, each radiation detection element In addition to the charges that are true image data generated by irradiation of radiation, dark charges are also read from the detection elements, and image data on which offsets due to dark charges are superimposed is read.

  Therefore, in order to obtain true image data by subtracting the offset due to dark charges from the read image data, it is formed with a thin film transistor (hereinafter referred to as TFT) or the like at the time of radiographic image capturing. The switch means is turned off for the same amount of time as the charge storage state in each radiation detection element when the switch means of each radiation detection element is turned off, but the radiation imaging apparatus is not irradiated with radiation. In some cases, a so-called offset correction value reading process (also referred to as a dark reading process) is performed in which the radiation image capturing apparatus is left unattended.

  In this offset correction value reading process, the TFT is turned off for the same time as radiographic imaging, so that the same amount of dark charge as that accumulated in each radiation detection element during radiographic imaging is applied to each radiation. It can be stored in the detection element, and by reading it, an offset amount (that is, an offset correction value) due to the dark charge superimposed on the true image data can be obtained. Then, true image data can be obtained by subtracting the offset correction value from the read image data.

  That is, for example, as shown in FIG. 28, in order to obtain the offset correction value O, when the TFT is turned off without irradiating the radiation imaging apparatus (see “TFToff” on the left side of the figure), each radiation detection is performed. Dark charges generated in the elements (see da in the figure) start to be accumulated in the respective radiation detection elements from that time, and the charge amount Q in each radiation detection element increases with time. In addition, Qa in the figure is a base charge accumulated in each radiation detection element, but this charge is not read out.

  Then, after the TFT is turned off for the same period of time as radiographic imaging, the TFT is turned on (see “TFTon” in the figure), the offset correction value reading process is started, and the TFT is turned off. Until the image reading process is completed (see “TFToff” on the right side of the figure), the charge O indicated by the oblique lines in the figure is read as the offset correction value O.

  Also, in radiographing, for example, as shown in FIG. 29, dark charges generated in each radiation detection element (see “TFToff” on the left side in the figure) when the TFT is turned off (see the left side in the figure). (See da)) starts to be accumulated in each radiation detection element, and the charge amount Q in each radiation detection element increases with time. When the radiation image capturing apparatus is irradiated with radiation, charges are generated in each radiation detection element during that time, and the charges are also accumulated in each radiation detection element.

  After the radiation irradiation is finished, the TFT is turned on (see “TFTon” in the figure), the image reading process is started, the TFT is turned off, and the image reading process is finished (in the figure). Until the right side (see “TFToff”), the charge d in the hatched portion in the figure is read out as image data d.

However, since the image data d read from the radiation detection element includes the offset correction value O caused by the dark charges described above, the true image data d generated by radiation irradiation in radiographic imaging. ^* Basically,
d ^* = d−O (1)
As described above, the offset correction value O can be subtracted from the read image data d.

JP-A-9-73144 JP 2006-58124 A JP-A-6-342099 JP 2007-260027 A

However, according to the study by the present inventors, in the case of continuous shooting or long shooting as described above in which a plurality of radiographic images are continuously captured in a short time using a radiographic imaging device, The image data d read out for each radiographic image capturing in the long image capturing includes not only the offset correction value O due to the dark charge as described above, but also image data d (or the image data previously captured in the same continuous capturing etc.) (or It has been found that an afterimage resulting from the true image data d ^* ), that is, an offset Olag due to a so-called lag may be superimposed.

  And even if the dark charge remains in each radiation detection element without being read out at the time of the image readout process, the shortage of each radiation detection element during each radiographic image capture in continuous imaging or long imaging The lag lag is not easily removed even if the reset process of each radiation detection element is repeatedly performed during a short interval, and the subsequent image reading is performed. It is known that an offset amount Olag appears during processing.

  The reason why the lag lag does not disappear easily even after repeated reset processing of each radiation detection element is that some of the electrons and holes generated in the radiation detection element due to radiation irradiation are a kind of metastable energy level (metastable It is considered that the state in which the mobility in the radiation detection element is lost is maintained for a relatively long time.

  And the electrons and holes in this metastable energy state are not always in the metastable energy level, and the electrons and holes whose energy level is lowered and mobility is restored appear little by little. It is considered that an offset image Olag due to an afterimage, that is, a lag, appears during the reading process of the image data d obtained by radiographic imaging.

  Then, as shown in FIG. 30, since the lag lag remains even if the reset process is repeated after the first imaging, the TFT is turned on after the radiation is irradiated in the second imaging, and the image is read out. During the period from the start of processing until the TFT is turned off and the image reading process is completed, the charge in the hatched portion d in the figure is read as image data d. Includes the charge indicated by the hatched portion O in the figure as the offset correction value O described above, and also includes the offset Olag due to the lag lag.

  Similarly, although not shown, for example, when the third shooting is performed, the image data d of the third shooting includes the lag lag generated in the first shooting in addition to the offset correction value O. In addition to the offset amount Olag, the offset amount Olag due to the lag lag generated in the second shooting is also superimposed. In this way, the offset Olag due to the lag lag generated in the previous imaging is superimposed on the image data read from each radiation detection element in the second and subsequent imaging.

  Further, it is understood that the offset Olag due to the lag lag becomes larger as the radiation dose irradiated to the radiation detecting element irradiated with the strong radiation increases in the photographing performed before the continuous photographing or the long photographing. ing.

  As described above, when the offset Olag due to the lag lag generated in the previous radiographic imaging in the continuous imaging or the long imaging is superimposed on the image data d obtained in the current radiographic imaging, the current radiographic imaging is performed. The image obtained in the above is in a state in which an afterimage due to the lag lag generated in the previous radiographic image capturing is reflected in the original image due to the current radiographic image capturing. For example, in the case of long imaging, an afterimage of the chest image taken before that is reflected in the waist image of the subject imaged in this radiographic imaging.

  For this reason, the obtained radiographic image becomes very difficult to see. For example, when a radiographic imaging device is used to capture a radiographic image for medical use, a doctor who viewed such a radiographic image overlooks the lesion. Or, there is a risk of misdiagnosis if there is a lesion in a non-lesioned portion.

  Therefore, when continuous imaging or long imaging is performed using a radiographic image capturing apparatus, the offset Olag due to the lag lag generated in the previous imaging can be accurately excluded from the image data d obtained by each radiographic image capturing. It is desirable to be configured as follows.

  As a method for eliminating the offset Olag due to the lag lag generated in the previous imaging, for example, as shown in the timing chart of FIG. 31, radiographic imaging is performed for each radiographic imaging in continuous imaging or long imaging. It is conceivable that the offset correction value reading process (also referred to as dark reading process) is performed immediately after it is performed.

  That is, radiographic imaging (A) is performed with the TFT turned off as described above, image readout processing (B) for reading image data d from each radiation detection element is performed, and reset processing (C) for each radiation detection element is performed. And after leaving the TFT in the off state for the same time as radiographic imaging (D), an offset correction value reading process (E) is performed. And the reset process (F) of each radiation detection element is performed as many times as necessary. Further, each of the processes A to F is performed for each radiographic image capturing.

If comprised in this way, in each offset correction value read-out process after radiographic imaging, since not only the offset correction value O by dark charge but the offset part Olag by lag lag is also read, according to the following (2) formula, By subtracting the total of the offset correction value O read out in each offset correction value reading process and the offset amount Olag by the lag lag from the image data d read out for each radiographic image capturing, each radiographic image It is possible to accurately obtain true image data d ^* for each photographing.

d ^* = d− (O + Olag) (2)
However, in this case, as described above, for each series of radiographic imaging performed in continuous imaging or long imaging, the TFT is turned off for the same period of time as radiographic imaging for each radiographic imaging, and the apparatus is left (D). In addition, since it is indispensable to perform the reset process (C) of each radiographic imaging apparatus for the offset correction value reading process for each radiographic image capture, the interval time between each radiographic image capture Becomes longer. For this reason, the time required for continuous imaging and long imaging for performing a series of radiographic imaging is increased as a whole, and this places a burden on the subject who is the subject.

  For example, as shown in FIG. 31, in the case of continuously performing radiographic imaging three times in continuous imaging or long imaging, the subject is at least from the first radiographic imaging to the final radiographic imaging (in the figure T)), it must be restrained in a state in which it cannot be separated from the radiographic image capturing apparatus. However, if the time required from the first radiographic image capture to the final radiographic image capture becomes longer, the burden on the subject is increased accordingly. It will be over.

  Therefore, when continuous imaging or long imaging is performed using a radiographic image capturing apparatus, it is possible to accurately exclude the offset Olag due to the lag lag from the image data d as described above, between each radiographic image capturing. It is desired that the interval be made as short as possible so that continuous shooting and long shooting can be completed in a shorter time.

  The present invention has been made in view of the above-described problems, and when performing continuous shooting or long shooting, the interval between each shooting can be shortened, and the offset due to the lag is accurately eliminated from the image data. An object of the present invention is to provide a possible radiographic imaging apparatus and a radiographic imaging system using the same.

In order to solve the above-described problem, the radiographic imaging device of the present invention includes:
A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; ,
A readout circuit that reads out charges accumulated in each of the radiation detection elements through the signal lines;
An off state and an on state are switched according to a voltage applied to the connected scanning line, arranged for each radiation detection element, and in the off state, the charge generated in the radiation detection element is retained, Switch means for releasing the charge from the radiation detection element in the ON state;
Scanning drive means for switching a voltage applied to the switch means via the scanning line between an on voltage and an off voltage;
Control means for controlling at least the readout circuit and the scanning drive means to perform readout processing of the charges from the radiation detection elements;
With
The control means reads out the offset correction value read out as an offset correction value after storing the radiation detecting element in a state where the radiation detecting element is not irradiated with radiation for a predetermined time before radiographic imaging. Immediately after the processing is performed, a lag readout process for reading out the electric charge remaining in each of the radiation detection elements as lag data is performed, and each time radiographic imaging is performed, depending on the dose of irradiated radiation. The image reading process for reading out the electric charge accumulated in each of the radiation detection elements as image data and the lag reading process immediately after that are performed in the same manner and timing as the offset correction value reading process and the lag reading process immediately after that. It is characterized by performing each by.

Moreover, the radiographic imaging device of the present invention is
A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; ,
A readout circuit that reads out charges accumulated in each of the radiation detection elements through the signal lines;
An off state and an on state are switched according to a voltage applied to the connected scanning line, arranged for each radiation detection element, and in the off state, the charge generated in the radiation detection element is retained, Switch means for releasing the charge from the radiation detection element in the ON state;
Scanning drive means for switching a voltage applied to the switch means via the scanning line between an on voltage and an off voltage;
Control means for controlling at least the readout circuit and the scanning drive means to perform readout processing of the charges from the radiation detection elements;
A sensor panel comprising:
Moving means for relatively displacing the positional relationship between the sensor panel and the subject;
With
The control means reads out the offset correction value read out as an offset correction value after storing the radiation detecting element in a state where the radiation detecting element is not irradiated with radiation for a predetermined time before radiographic imaging. Immediately after the processing is performed, a lag readout process for reading out the electric charge remaining in each of the radiation detection elements as lag data is performed, and then the relative positional relationship between the sensor panel and the subject is determined by the moving means. Each time a radiographic image is taken while being displaced, an image readout process for reading out the electric charge accumulated in each of the radiation detection elements as image data in accordance with the dose of the irradiated radiation, and a lag readout process immediately after that, The same processing method and timing as the offset correction value reading process and the lag reading process immediately after the offset correction value reading process And carrying out, respectively.

Moreover, the radiographic imaging system of the present invention is
A radiographic imaging apparatus of the present invention comprising a communication means capable of transmitting and receiving information;
A radiation generator comprising a radiation source for irradiating the radiation imaging apparatus with radiation;
The image data read from the image reading process, the offset correction value read by the offset correction value reading process, and the lag reading immediately after the image reading process transmitted from the radiation image capturing apparatus Based on the lag data read in the process and the lag data read in the lag read process immediately after the offset correction value read process, the difference between the image data and the offset correction value, A console for calculating true image data for each radiation detection element by subtracting the difference between the lag data read in the lag readout process immediately after the image readout process and the offset correction value readout process. When,
It is characterized by providing.

  According to the radiographic imaging apparatus and radiographic imaging system of the system as in the present invention, before a series of radiographic imaging of continuous imaging or long imaging, the apparatus is left for a predetermined time without radiation, An offset correction value reading process for reading an offset correction value from the radiation detection element is performed, and a lag reading process is performed immediately thereafter. Further, in a series of radiographic imaging such as continuous imaging or long imaging, every time radiographic imaging is performed, image readout processing for reading out image data from each radiation detection element is performed, and lag readout processing is performed immediately thereafter.

  At that time, the image reading process and the immediately following lag reading process are performed in the same manner and timing as the offset correction value reading process before radiographic image capturing and the immediately following lag reading process.

  Therefore, in each radiographic imaging in continuous imaging or long imaging, a lag lag occurs in radiographic imaging before that, and the lag lag is removed even if the reset processing of each radiation detection element is repeated during each radiographic imaging. Even if the image data d includes the offset Olag due to the lag lag generated in the previous radiographic image capturing, the image data d uses the lag data Ld read out by the lag readout processing, etc. It is possible to accurately eliminate the offset Olag caused by the lag lag from the data d.

  Then, after accurately eliminating the offset Olag caused by the lag lag from the image data d, the offset correction value O read out by the offset correction value reading process is further subtracted, thereby obtaining a true value for each radiation detection element. Image data can be calculated accurately.

  Further, according to the radiographic image capturing apparatus and radiographic image capturing system of the system as in the present invention, each radiographic image for the offset correction value reading process for each radiographic image capture as in the conventional method (see FIG. 31). Since it is not necessary to reset the imaging device (C) or leave the device (D) with the TFT turned off for the same time as radiographic imaging, the interval between radiographic imaging can be shortened. Therefore, it is possible to reduce the time required for continuous imaging and long imaging in which a series of radiographic imaging is repeated.

  Therefore, the time T during which the subject who is the subject must be restrained in a state in which the subject cannot be separated from the radiographic imaging apparatus at least from the first radiographic imaging to the final radiographic imaging is set as compared with the conventional method. It becomes possible to shorten and to reduce the burden placed on the subject.

It is a perspective view which shows the structure of the radiographic imaging apparatus which concerns on each embodiment. It is sectional drawing which follows the XX line in FIG. It is a top view which shows the structure of the board | substrate of the sensor panel of a radiographic imaging apparatus. It is an enlarged view which shows the structure of the radiation detection element, TFT, etc. which were formed in the small area | region on the board | substrate of the sensor panel of FIG. It is sectional drawing which follows the YY line in FIG. It is a side view explaining the sensor panel formed by attaching COF, a PCB board, etc. to a board. It is a block diagram showing the equivalent circuit of the sensor panel of a radiographic imaging apparatus. It is a block diagram showing the equivalent circuit about 1 pixel which comprises the detection part of a sensor panel. It is a timing chart which shows the timing which switches the voltage applied to each scanning line between ON voltage and OFF voltage in the reset process of each radiation detection element. 5 is a timing chart showing timings at which a voltage applied to each scanning line is switched between an on voltage and an off voltage in image reading processing, offset correction value reading processing, and the like. It is a figure which shows the whole structure of the radiographic imaging system which concerns on each embodiment. (A) is a figure which shows the structure of an operation switch, (B) is a state which the button part was half-pressed, (C) is a figure explaining the state by which the button part was fully pressed. It is the schematic which shows the structure of the elongate imaging device which concerns on each embodiment. It is the schematic which shows another structural example of a elongate imaging device. It is a timing chart in the case of performing each process with the control method which concerns on 1st Embodiment in continuous imaging | photography or long imaging | photography. It is a timing chart which shows the timing which switches the voltage applied to each scanning line between the on voltage and the off voltage in the lag readout process in the first embodiment. It is a graph explaining the reference | standard lag data read by the offset correction value read by an offset correction process, and the lag read process immediately after that. It is a timing chart showing each timing of reception of an irradiation start signal, reset processing for one surface, transmission of an interlock release signal, and irradiation of radiation. It is a graph explaining the method of calculating true image data from the image data read by the image read-out process after the n-th radiographic imaging in continuous imaging or long imaging. It is a figure explaining the timing chart in the case of performing each process with the control method which concerns on 1st Embodiment in continuous imaging | photography or long imaging | photography, and the time to restrain a test subject. 10 is a timing chart in a case where an on-voltage is configured to be simultaneously applied to a predetermined number of scanning lines in the lag readout process of the second embodiment. FIG. 22 is a diagram illustrating that when configured as in FIG. 21, the total value of electric charges discharged from each radiation detection element is accumulated in the capacitor of the amplifier circuit. It is a figure explaining that the electric charge discharge | released from the several radiation detection element connected to the signal line adjacent when it has a binning mode is also accumulate | stored in the capacitor | condenser of an amplifier circuit. It is a timing chart explaining the time which a lag read-out process is shortened in 2nd Embodiment, and the time which restrains a test subject is further shortened. FIG. 22 is a diagram for explaining the calculation of lag data for each radiation detection element by performing an interpolation process or the like when configured as in FIG. 21. It is a timing chart at the time of comprising so that an ON voltage may be applied to the scanning line selected in the lag read-out process in the modification of 2nd Embodiment. It is a timing chart at the time of having comprised so that it may be varied so that ON time may become short in the modification of 2nd Embodiment, and a lag read-out process is performed. It is a graph explaining the dark charge which generate | occur | produces and accumulate | stores in each radiation detection element, and the offset correction value read by an offset correction process. It is a graph explaining the change of the electric charge amount in each radiation detection element at the time of radiographic imaging, the image data read by image read-out processing, and the offset correction value contained in it. It is a graph explaining the lag remaining after radiographic imaging, the image data read by the image reading process, and the offset correction and the offset due to the lag included therein. It is a figure explaining the timing chart in the case of performing each process with the conventional control method in continuous imaging | photography or long imaging | photography, and the time to restrain a test subject.

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

[First Embodiment]
[Configuration of Radiation Imaging System]
The above-described radiographic image capturing apparatus that performs long imaging for capturing a wide range of the subject's body while changing the position of the radiographic image capturing apparatus with respect to the subject will be described later. A radiographic imaging apparatus capable of continuous imaging in which the radiographic imaging apparatus performs imaging while changing the orientation of a subject as a subject will be described.

  In the following, a radiographic image capturing apparatus that performs long imaging is referred to as a long imaging apparatus when distinguished from a radiographic image capturing apparatus that performs continuous imaging.

  In the following, a radiographic imaging apparatus that performs continuous imaging or long imaging includes a scintillator or the like, and converts the irradiated radiation into electromagnetic waves of other wavelengths such as visible light to obtain an electrical signal. Although the case of a radiographic imaging apparatus will be described, the present invention can also be applied to a direct type radiographic imaging apparatus.

  Furthermore, although the case where the radiographic imaging apparatus which performs continuous imaging | photography is portable below is demonstrated, it is applied also to what is called a stationary radiographic imaging apparatus formed integrally with a support stand etc.

  FIG. 1 is an external perspective view of a radiographic imaging apparatus according to the first embodiment of the present invention, and FIG. 2 is a cross-sectional view taken along line XX of FIG. As shown in FIGS. 1 and 2, the radiographic imaging apparatus 1 according to the present embodiment is configured by housing a sensor panel Sp including a scintillator 3, a substrate 4, and the like in a housing 2.

  The housing 2 is formed of a material such as a carbon plate or plastic that at least the radiation incident surface R transmits radiation. 1 and 2 show a case in which the housing 2 is a so-called lunch box type formed by the frame plate 2A and the back plate 2B. However, the housing 2 is integrally formed in a rectangular tube shape. It is also possible to use a so-called monocoque type.

  As shown in FIG. 1, the side surface of the housing 2 is opened and closed for replacement of a power switch 36, an indicator 37 composed of LEDs and the like, and a battery 41 (not shown) (see FIG. 7 described later). A possible lid member 38 and the like are arranged. In the present embodiment, the side surface of the lid member 38 has communication means for transmitting and receiving information such as image data d wirelessly with an external device such as a console 58 (see FIG. 11) described later. An antenna device 39 is embedded.

  The installation position of the antenna device 39 is not limited to the side surface portion of the lid member 38, and the antenna device 39 can be installed at an arbitrary position of the radiographic image capturing apparatus 1. The number of antenna devices 39 to be installed is not limited to one, and a plurality of antenna devices 39 may be provided. Furthermore, information such as image data d can also be configured to be transmitted / received to / from an external device in a wired manner. In this case, for example, as a communication means, a LAN (Local Area Network) cable, USB ( (Universal Serial Bus) A connection terminal or the like for connecting a cable or the like is provided on the side surface of the radiation image capturing apparatus 1 or the like.

  As shown in FIG. 2, a base 31 is disposed inside the housing 2 via a lead thin plate (not shown) on the lower side of the substrate 4 of the sensor panel Sp. A PCB substrate 33, a buffer member 34, and the like on which are disposed are mounted. In the present embodiment, a glass substrate 35 for protecting the substrate 4 and the radiation incident surface R of the scintillator 3 is disposed.

  The scintillator 3 is attached to a detection unit P, which will be described later, of the substrate 4. As the scintillator 3, for example, a scintillator 3 that has a phosphor as a main component and converts it into an electromagnetic wave having a wavelength of 300 to 800 nm, that is, an electromagnetic wave centered on visible light when it receives incident radiation, is used.

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

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

  In the present embodiment, a photodiode is used as the radiation detection element 7, but other than this, for example, a phototransistor or the like can also be used. Each radiation detection element 7 is connected to the source electrode 8s of the TFT 8 serving as a switch means, as shown in the enlarged views of FIGS. The drain electrode 8 d of the TFT 8 is connected to the signal line 6.

  The TFT 8 is turned on when a turn-on voltage is applied to the connected scanning line 5 by the scanning drive means 15 described later, and is applied to the gate electrode 8g, and is stored in the radiation detection element 7. The electric charge that is present is emitted to the signal line 6. Further, the TFT 8 is turned off when the off voltage is applied to the connected scanning line 5 and the off voltage is applied to the gate electrode 8g, and the emission of the charge from the radiation detecting element 7 to the signal line 6 is stopped. The charges generated in the radiation detection element 7 are held and accumulated in the radiation detection element 7.

  Here, the structure of the radiation detection element 7 and the TFT 8 in this embodiment will be briefly described with reference to the cross-sectional view shown in FIG. FIG. 5 is a cross-sectional view taken along line YY in FIG.

A gate electrode 8g of a TFT 8 made of Al, Cr or the like is formed on the surface 4a of the substrate 4 so as to be integrally laminated with the scanning line 5, and silicon nitride (laminated on the gate electrode 8g and the surface 4a). The first electrode 74 of the radiation detecting element 7 is connected to the upper portion of the gate electrode 8g on the gate insulating layer 81 made of SiN _x ) or the like via the semiconductor layer 82 made of hydrogenated amorphous silicon (a-Si) or the like. The formed source electrode 8s and the drain electrode 8d formed integrally with the signal line 6 are laminated.

The source electrode 8s and the drain electrode 8d are divided by a first passivation layer 83 made of silicon nitride (SiN _x ) or the like, and the first passivation layer 83 covers both electrodes 8s and 8d from above. In addition, ohmic contact layers 84a and 84b formed in an n-type by doping hydrogenated amorphous silicon with a group VI element are stacked between the semiconductor layer 82 and the source electrode 8s and the drain electrode 8d, respectively. The TFT 8 is formed as described above.

  In the radiation detecting element 7, an auxiliary electrode 72 is formed by laminating Al, Cr, or the like on the insulating layer 71 formed integrally with the gate insulating layer 81 on the surface 4 a of the substrate 4. A first electrode 74 made of Al, Cr, Mo or the like is laminated on the auxiliary electrode 72 with an insulating layer 73 formed integrally with the first passivation layer 83 interposed therebetween. The first electrode 74 is connected to the source electrode 8 s of the TFT 8 through the hole H formed in the first passivation layer 83.

  On the first electrode 74, an n layer 75 formed in an n-type by doping a hydrogenated amorphous silicon with a group VI element, an i layer 76 which is a conversion layer formed of hydrogenated amorphous silicon, and a hydrogenated amorphous A p layer 77 formed by doping a group III element into silicon and forming a p-type layer is formed by laminating sequentially from below.

  At the time of radiographic imaging, radiation enters from the radiation incident surface R of the housing 2 of the radiographic imaging apparatus 1 and is converted into electromagnetic waves such as visible light by the scintillator 3, and the converted electromagnetic waves are irradiated from above in the figure. Then, the electromagnetic wave reaches the i layer 76 of the radiation detection element 7, and electron-hole pairs are generated in the i layer 76. In this way, the radiation detection element 7 converts the electromagnetic waves irradiated from the scintillator 3 into electric charges.

  On the p layer 77, a second electrode 78 made of a transparent electrode such as ITO is laminated and formed so that the irradiated electromagnetic wave reaches the i layer 76 and the like. In the present embodiment, the radiation detection element 7 is formed as described above. The order of stacking the p layer 77, the i layer 76, and the n layer 75 may be reversed. Further, in the present embodiment, a case where a so-called pin-type radiation detection element formed by sequentially stacking the p layer 77, the i layer 76, and the n layer 75 as described above is used as the radiation detection element 7. However, it is not limited to this.

A bias line 9 for applying a bias voltage to the radiation detection element 7 is connected to the upper surface of the second electrode 78 of the radiation detection element 7 via the second electrode 78. The second electrode 78 and the bias line 9 of the radiation detection element 7, the first electrode 74 extended to the TFT 8 side, the first passivation layer 83 of the TFT 8, that is, the upper surfaces of the radiation detection element 7 and the TFT 8 are A second passivation layer 79 made of silicon nitride (SiN _x ) or the like is covered from above.

  As shown in FIGS. 3 and 4, in this embodiment, one bias line 9 is connected to a plurality of radiation detection elements 7 arranged in rows, and each bias line 9 is connected to a signal line 6. Are arranged in parallel with each other. Further, each bias line 9 is bound to the connection 10 at a position outside the detection portion P of the substrate 4.

  In this embodiment, as shown in FIG. 3, each scanning line 5, each signal line 6, and connection 10 of the bias line 9 are input / output terminals (also referred to as pads) provided near the edge of the substrate 4. 11 is connected. As shown in FIG. 6, each input / output terminal 11 has a COF (Chip On Film) 12 in which a chip such as a gate IC 12 a constituting a gate driver 15 b of the scanning drive unit 15 described later is formed on a film. They are connected via an anisotropic conductive adhesive material 13 such as an anisotropic conductive adhesive film or an anisotropic conductive paste.

  The COF 12 is routed to the back surface 4b side of the substrate 4 and connected to the PCB substrate 33 described above on the back surface 4b side. In the present embodiment, the sensor panel Sp of the radiographic image capturing apparatus 1 is formed as described above. In FIG. 6, illustration of the electronic component 32 and the like is omitted.

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

  As described above, each radiation detection element 7 of the detection unit P of the sensor panel Sp has the bias line 9 connected to the second electrode 78, and each bias line 9 is bound to the connection 10 to be the bias power supply 14. It is connected to the. The bias power supply 14 applies a bias voltage to the second electrode 78 of each radiation detection element 7 via the connection 10 and each bias line 9. The bias power source 14 is connected to a control unit 22 described later, and the control unit 22 controls a bias voltage applied to each radiation detection element 7 from the bias power source 14.

  As shown in FIGS. 7 and 8, in this embodiment, it can be seen that the bias line 9 is connected via the second electrode 78 to the p-layer 77 side (see FIG. 5) of the radiation detection element 7. In addition, the bias power supply 14 supplies a voltage equal to or lower than a voltage applied to the second electrode 78 of the radiation detection element 7 via the bias line 9 as a bias voltage on the first electrode 74 side of the radiation detection element 7 (that is, a so-called reverse bias voltage). Is applied.

  The first electrode 74 of each radiation detection element 7 is connected to the source electrode 8s of the TFT 8 (indicated as S in FIGS. 7 and 8), and the gate electrode 8g of each TFT 8 (FIGS. 7 and 8). Are respectively connected to the lines L1 to Lx of the scanning line 5 extending from the gate driver 15b of the scanning driving means 15 to be described later. Further, the drain electrode 8 d (denoted as D in FIGS. 7 and 8) of each TFT 8 is connected to each signal line 6.

  The scanning drive means 15 is a power supply circuit 15a that supplies an on voltage and an off voltage to the gate driver 15b via the wiring 15c, and a voltage applied to each line L1 to Lx of the scanning line 5 between the on voltage and the off voltage. A gate driver 15b that switches between the on state and the off state of each TFT 8 is provided.

  Then, the scanning drive unit 15 performs reset processing of each radiation detection element 7 that discharges charges remaining in each radiation detection element 7, image read processing for reading image data d from each radiation detection element 7, and the like. When a trigger signal is received from the control means 22 to be described later, switching between the on-voltage and the off-voltage of the voltage applied to each line L1 to Lx of the scanning line 5 from the gate driver 15b is started.

  In the present embodiment, when the scanning drive unit 15 receives the trigger signal from the control unit 22 during the reset process of each radiation detection element 7, for example, as shown in FIG. 9, the scan drive unit 15 applies the trigger signal from the gate driver 15b. The lines L1 to Lx of the scanning line 5 for switching the voltage between the on voltage and the off voltage are sequentially switched to perform the reset process Rm for one surface, and the reset process Rm for the one surface is repeatedly performed as necessary. The reset processing of each radiation detection element 7 is performed while adjusting them.

  In the present embodiment, the scanning drive unit 15 receives a trigger signal from the control unit 22 during an image reading process, an offset correction value reading process, and a lag reading process, which will be described later, for example, as shown in FIG. In addition, the lines L1 to Lx of the scanning line 5 for switching the voltage applied from the gate driver 15b between the on voltage and the off voltage are sequentially switched, and connected to the lines L1 to Lx of the scanning line 5 through the TFTs 8. The image data d, the offset correction value O, the lag data Ld, and the like are read from each of the radiation detection elements 7 that are provided. Note that the lag data Ld is data read from each radiation detection element 7 in the lag reading process.

  As shown in FIGS. 7 and 8, each signal line 6 is connected to each readout circuit 17 formed in the readout IC 16. In the present embodiment, the readout IC 16 is provided with one readout circuit 17 for each signal line 6.

  The readout circuit 17 includes an amplification circuit 18 and a correlated double sampling circuit 19. An analog multiplexer 21 and an A / D converter 20 are further provided in the reading IC 16. 7 and 8, the correlated double sampling circuit 19 is represented as CDS. In FIG. 8, the analog multiplexer 21 is omitted.

  In the present embodiment, the amplifier circuit 18 is configured by a charge amplifier circuit, and is configured by connecting a capacitor 18b and a charge reset switch 18c in parallel to the operational amplifier 18a and the operational amplifier 18a. In addition, a power supply unit 18 d for supplying power to the amplifier circuit 18 is connected to the amplifier circuit 18.

Further, the signal line 6 is connected to the inverting input terminal on the input side of the operational amplifier 18 a of the amplifier circuit 18, and the reference potential V ₀ is applied to the non-inverting input terminal on the input side of the amplifier circuit 18. ing. Note that the reference potential V ₀ is set to an appropriate value, and in this embodiment, for example, 0 [V] is applied.

  The charge reset switch 18 c of the amplifier circuit 18 is connected to the control means 22, and is turned on / off by the control means 22. At the time of image reading processing from each radiation detection element 7, if the TFT 8 of the radiation detection element 7 is turned on while the charge reset switch 18 c is off, the charge released from each radiation detection element 7 is transferred to the signal line 6. The voltage value corresponding to the accumulated charge amount is output from the output side of the operational amplifier 18a.

  In this way, the amplifier circuit 18 outputs a voltage value according to the amount of charge output from each radiation detection element 7 and converts the charge voltage. When the charge reset switch 18c is turned on, the input side and the output side of the amplifier circuit 18 are short-circuited, and the charge accumulated in the capacitor 18b is discharged to reset the amplifier circuit 18. ing. Note that the amplifier circuit 18 may be configured to output a current in accordance with the charge output from the radiation detection element 7.

  A correlated double sampling circuit (CDS) 19 is connected to the output side of the amplifier circuit 18. In this embodiment, the correlated double sampling circuit 19 has a sample and hold function. The sample and hold function in the correlated double sampling circuit 19 is turned on / off by a pulse signal transmitted from the control means 22. To be controlled.

  Then, the control means 22 controls the amplification circuit 18 and the correlated double sampling circuit 19 in the image reading process from each radiation detection element 7 after radiographic imaging, and the electric charge discharged from each radiation detection element 7. Is subjected to charge-voltage conversion by the amplifier circuit 18, and the voltage value subjected to the charge-voltage conversion is sampled by the correlated double sampling circuit 19 and output to the downstream side as image data d.

  The image data d of each radiation detection element 7 output from the correlated double sampling circuit 19 is transmitted to the analog multiplexer 21 (see FIG. 7), and is sequentially transmitted from the analog multiplexer 21 to the A / D converter 20. Then, the A / D converter 20 sequentially converts the image data d into digital values, outputs them to the storage means 40, and sequentially stores them.

  Each image data d read from each radiation detection element 7 is stored in an image storage area (not shown) of the storage means 40 in accordance with an instruction of a memory controller (not shown) controlled by the control means 22. .

  The control means 22 includes a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), an input / output interface connected to the bus, an FPGA (Field Programmable Gate Array), or the like (not shown). It is configured. It may be configured by a dedicated control circuit. And the control means 22 controls operation | movement etc. of each member of the radiographic imaging apparatus 1. Further, as shown in FIG. 7 and the like, the control means 22 is connected with a storage means 40 composed of a DRAM or the like.

  In the present embodiment, the above-described antenna device 39 is connected to the control unit 22, and each member such as the detection unit P, the scanning drive unit 15, the readout circuit 17, the storage unit 40, the bias power supply 14, and the like. A battery 41 for supplying electric power is connected. The battery 41 is provided with a connection terminal 42 for charging the battery 41 by supplying power to the battery 41 from a charging device (not shown) such as a cradle.

  As described above, the control means 22 controls the bias power supply 14 to set a bias voltage to be applied to each radiation detection element 7 from the bias power supply 14, or the charge reset switch 18 c of the amplification circuit 18 of the readout circuit 17. Various processes such as on / off control and transmission of a pulse signal to the correlated double sampling circuit 19 to control on / off of the sample hold function are executed.

  Further, the control means 22 scans the driving means at the time of reset processing of each radiation detection element 7, at the time of image reading processing from each radiation detection element 7 after radiographic imaging, at the time of offset correction value reading processing, at the time of lag reading processing. 15, a signal instructing which process to perform is transmitted as a trigger signal for starting those processes. As a signal for instructing the process, a different signal is transmitted in each of the above processes.

  In addition, when the scanning drive unit 15 receives a signal instructing processing from the control unit 22 as a trigger signal, the scanning detection unit 15 resets each radiation detection element 7 at the timing shown in FIG. When the offset correction value reading process or the lag reading process is performed, for example, the voltages applied from the gate driver 15b to the lines L1 to Lx of the scanning line 5 are set to the ON voltage and the OFF voltage at the timing shown in FIG. The lines L1 to Lx of the scanning line 5 to which the ON voltage is applied are sequentially switched.

  Note that the timing at which the voltage applied from the gate driver 15b of the scanning drive unit 15 to each of the lines L1 to Lx of the scanning line 5 is switched between the on-voltage and the off-voltage during the lag readout processing is the timing shown in FIG. It is possible to configure the timing to be different, but this will be described later.

  In addition, regarding the control configuration of each process of the radiation detection element 7 in the control unit 22 such as reset processing, image readout processing, offset correction value readout processing, and lag readout processing, the configuration of the radiation imaging system 50 or long imaging is performed. The configuration of the radiation image capturing apparatus (that is, the above-described long image capturing apparatus) 100 to be performed will be described later.

[Configuration of radiation imaging system]
FIG. 11 is a diagram illustrating an overall configuration of the radiographic image capturing system according to the present embodiment. As shown in FIG. 11, the radiographic imaging system 50 includes, for example, an imaging room R1 that irradiates radiation and images a subject (part of the patient's imaging target) that is a part of a patient (not shown), and a radiographer or the like. The anterior chamber R2 where the operator performs various operations such as control of the start of radiation applied to the subject, and the outside thereof are arranged.

  In the radiographing room R1, a bucky device 51 that can be loaded with the radiographic imaging device 1 described above, a radiation source 52 that includes an X-ray tube (not shown) that generates radiation to irradiate a subject, and a radiation generation device 55 that controls the radiation source In addition, when the radiographic image capturing apparatus 1 and the radiation generating apparatus 55 and the console 58 communicate wirelessly, a base station 54 provided with a wireless antenna 53 that relays these communications is provided.

  11 shows a case where the portable radiographic imaging device 1 is used by being loaded into the cassette holding part 51a of the bucky device 51. However, as described above, the radiographic imaging device 1 is used as the bucky device 51. Or may be formed integrally with a support base or the like. Further, as described above, when communication between the radiographic imaging apparatus 1 and an external apparatus is performed via a cable such as a LAN cable, these cables are connected to the base station 54 as shown in FIG. It is also possible to configure such that information such as data can be transmitted / received by wired communication via a cable or the base station 54.

  The base station 54 is connected to the radiation generating device 55 and the console 58, and signals for LAN communication when transmitting information between the radiographic image capturing device 1 and the console 58 are transmitted to the base station 54. Is converted into a signal for transmitting information to and from the radiation generating device 55, and a converter (not shown) that performs the reverse conversion is incorporated.

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

  For example, as shown in FIG. 12A, the exposure switch 56 includes a rod-shaped button portion 56a having a predetermined stroke, and a housing that supports the button portion 56a so as to be movable in the stroke direction indicated by an arrow S in the drawing. It is comprised with the body part 56b. The button part 56a of the exposure switch 56 includes, for example, a cylindrical part 56a1 protruding upward from the casing part 56b and a columnar part 56a2 protruding further upward from the inside thereof.

  Then, as shown in FIG. 12B, when the column portion 56a2 is pushed in the stroke direction S up to the upper end portion of the cylindrical portion 56a1 (that is, when a so-called half-press operation is performed), the exposure switch 56 is operated. An activation signal is transmitted to the radiation generator 55 via the table 57. Upon receiving this activation signal, the radiation generating device 55 places the radiation source 52 in a standby state by starting rotation of the anode of the X-ray tube of the radiation source 52.

  Further, as shown in FIG. 12C, when both the cylindrical portion 56a1 and the columnar portion 56a2 of the exposure switch 56 are pushed to the upper end portion of the housing portion 56b (that is, when a so-called full pushing operation is performed). The exposure switch 56 transmits an irradiation start signal to the radiation generator 55 via the console 57.

  When the radiation generation device 55 receives this irradiation start signal from the exposure switch 56, the radiation generation device 55 transmits the irradiation start signal to the radiographic imaging device 1 via the base station 54 by a wireless method or a wired method. Then, as will be described later, when receiving the interlock release signal transmitted from the radiographic imaging apparatus 1 via the base station 54, the radiation generation apparatus 55 emits radiation from the X-ray tube of the radiation source 52. It is like that.

  In addition to this, the radiation generating device 55 moves the radiation source 52 to a predetermined position so that the radiation image capturing device 1 loaded in the designated bucky device 51 can be appropriately irradiated with radiation, or the radiation direction thereof. Adjusting a diaphragm or a collimator (not shown) so that the radiation is irradiated in a predetermined region of the radiographic imaging apparatus 1, or adjusting the radiation source 52 so that an appropriate dose of radiation is irradiated. Various controls such as adjustment are performed on the radiation source 52. In addition, you may comprise so that operators, such as a radiographer, may perform these processes manually.

  In addition, the radiation generator 55 irradiates the radiation from the radiation source 52 by, for example, stopping the X-ray tube of the radiation source 52 when a predetermined time has elapsed from the start of radiation irradiation from the radiation source 52. Is supposed to stop.

  The configuration and the like of the radiographic image capturing apparatus 1 are as described above. However, in the present embodiment, the radiographic image capturing apparatus 1 may be used by being mounted on the bucky device 51 as described above. 51 is not loaded and can be used alone.

  That is, the radiation image photographing apparatus 1 is disposed on the upper surface side in a single state, for example, in a bed provided in the photographing room R1 or in a bucky device 51B for lying position photographing as shown in FIG. (See FIG. 1) The patient's hand, which is the subject, can be placed on the top, or the patient's waist, legs, etc. lying on the bed can be inserted between the bed and the bed. It has become. In this case, for example, radiation image capturing is performed by irradiating the radiation image capturing apparatus 1 with radiation from a portable radiation source 52B or the like via a subject.

  In the present embodiment, the radiographic image capturing apparatus 1 is loaded from the radiation source 52 of the radiation generating apparatus 55 with respect to the radiographic image capturing apparatus 1 while being loaded on the bucky apparatus 51 or placed on the bed. The subject can be continuously photographed by continuously irradiating radiation while changing the orientation of the body of the subject (not shown) that is the subject with respect to the irradiation direction of the radiation, or without changing the orientation or the like. It has become.

  In the present embodiment, the image data d is processed based on the image data d transmitted from the radiation image capturing apparatus 1, and is configured by a computer or the like that can generate a final radiation image. A console 58 is provided outside the imaging room R1 and the front room R2. It is also possible to configure the console 58 so as to be provided, for example, in the front chamber R2. In addition, the console 58 is connected to or includes a storage means 59 composed of an HDD (Hard Disk Drive) or the like.

  For example, a preview image based on the image data d acquired by radiographic imaging is displayed on the console 58, or the radiographic imaging apparatus 1 is set between a wake-up state and a sleep state. Or a function that allows an operator such as a radiographer to create or select imaging order information that represents the contents of radiographic imaging performed in the imaging room R1. It is also possible to configure so that it is configured appropriately.

[Configuration of long-length imaging device]
In addition, the radiographic image capturing apparatus 100 that performs long-length imaging in which, for example, a wide range of the subject's body is imaged while the positional relationship between the sensor panel Sp and the subject being the subject is relatively displaced in the imaging room R1, That is, it is possible to provide the long photographing apparatus 100.

  For example, as shown in FIG. 13, the long photographing apparatus 100 includes a sensor panel Sp, and a moving unit 101 that relatively displaces the positional relationship between the sensor panel Sp and the subject Hu. In the present embodiment, the long imaging device 100 is configured to move the sensor panel Sp housed inside the support 102. For example, the portable radiographic imaging device 1 described above is used. The radiographic image capturing apparatus 1 may be configured to be mounted on the long image capturing apparatus 100 and moved.

  The configuration of the sensor panel Sp is the same as that described in the configuration of the radiation image capturing apparatus 1 described above, and the description thereof is omitted. Hereinafter, each functional unit of the sensor panel Sp will be described using the same reference numerals as those used in the description of the radiographic image capturing apparatus 1 described above.

  In the present embodiment, the sensor panel Sp is housed integrally in the support body 102. The support 102 has, for example, a length longer than that of a general adult, and the moving unit 101 is used to move the sensor panel Sp along the longitudinal direction (the direction of the arrow shown in FIG. 13). A moving mechanism 101a and a moving mechanism control means 101b are provided.

  The moving mechanism 101a includes a motor or the like (not shown). Further, the moving mechanism control means 101b controls the start and stop of the moving mechanism 101a, and controls the moving mechanism 101a to move the sensor panel Sp so that it is within the photographing target range of the subject Hu. The positional relationship between the sensor panel Sp and the subject Hu is relatively displaced. Although the shooting target range of the subject Hu is different for each shooting, the moving unit 101 can move the sensor panel Sp within a range from a general adult's head to the tip of the foot so that any shooting can be handled. It is preferable that it is comprised.

  In FIG. 13, the sensor panel Sp is moved in the longitudinal direction of the support body 102 (that is, the vertical direction in this case), and the image is taken three times, thereby taking a long image from the head of the subject who is the subject Hu to the toes. However, the present invention is not limited to this, and the number of times of imaging performed by moving the sensor panel Sp in the longitudinal direction is appropriately set according to the vertical length of the sensor panel Sp, the distance to be moved, and the like. Is done.

  In this embodiment, the movement mechanism control means 101b is connected to the control means 22 on the sensor panel Sp in addition to the movement mechanism 101a, and the base station 54 (see FIG. 11) by a wired system such as a cable (not shown). It is connected to the.

  Then, as described above, when the irradiation start signal is transmitted from the radiation generator 55 that has received the irradiation start signal from the exposure switch 56 via the base station 54, the moving mechanism control unit 101b receives the irradiation start signal. Is transmitted to the control means 22 of the sensor panel Sp, and as will be described later, when an interlock release signal is received from the control means 22 of the sensor panel Sp, radiation is generated via the base station 54. The data is transmitted to the device 55.

  In the long photographing apparatus 100 of the present embodiment, data, signals, etc. between the sensor panel Sp and external devices such as the radiation generator 55 and the console 58 are thus provided via the moving mechanism control means 101b of the moving means 101. Therefore, the moving mechanism control unit 101b constitutes a communication unit capable of transmitting / receiving information to / from an external device. Therefore, in this case, it is not always necessary to provide the antenna device 39 on the sensor panel Sp.

  Further, FIG. 13 shows the standing long photographing apparatus 100 that performs photographing by raising the subject who is the subject Hu in front of the support 102, that is, the radiation source 52 side. For example, as shown in FIG. 14, a long-sided photographing apparatus 100 in a prone position that photographs a subject who is not shown in the lying state on the support 102 may be used.

  In the case of the upright long photographing apparatus 100, the sensor panel Sp housed in the support 102 or the loaded radiographic image photographing apparatus 1 is installed as in the case of the standing long photographing apparatus 100 shown in FIG. It is also possible to perform a plurality of photographing operations while moving the support body 102 in the longitudinal direction. Further, as shown in FIG. 14, the support 102 is configured to move in the longitudinal direction (for example, see the arrow in the figure) with respect to the sensor panel Sp and the radiographic imaging device 1 that are fixed in position, Alternatively, the support 102 and the sensor panel Sp and the radiation image capturing apparatus 1 can be both moved to relatively displace the positional relationship between the subject Hu and the sensor panel Sp.

[Control configuration of each process during continuous shooting and long shooting]
Hereinafter, each of the radiation detection elements 7 in the control means 22 of the sensor panel Sp when performing continuous imaging using the radiographic image capturing apparatus 1 or when performing long imaging using the long image capturing apparatus 100. The control configuration of each of the reset process, image read process, offset correction value read process, and lag read process will be described. The operation of the radiographic image capturing apparatus 1 (including the long image capturing apparatus 100) and the radiographic image capturing system 50 according to the present embodiment will also be described.

  In addition, the control configuration of each process in the control means 22 of the sensor panel Sp in the radiographic imaging apparatus 1 and the control configuration of each process in the control means 22 of the sensor panel Sp in the long imaging apparatus 100 are basically. These are the same, and will be described together below. However, it goes without saying that continuous shooting and long shooting are not performed simultaneously.

  FIG. 15 is a timing chart in the case where each process is performed by the control method according to the present embodiment in continuous shooting or long shooting, but for easy comparison with each process shown in the timing chart of FIG. The same processes as those in FIG. 31 will be described with the same symbols.

  In the present embodiment, the control means 22 of the sensor panel Sp of the radiographic imaging device 1 or the long imaging device 100 is activated by pressing the power switch 36 (see FIG. 1) prior to radiographic imaging. When the state of the sensor panel Sp is changed to an awake state by an instruction from the console 58, or when a signal to start resetting of each radiation detection element 7 is received from the console 58, each radiation detection element 7 (see “Reset” at the left end of FIG. 15).

  In the reset process of each radiation detection element 7, as described above, the control unit 22 transmits a signal instructing the reset process of each radiation detection element 7 as a trigger signal to the scanning drive unit 15. Upon receiving this trigger signal, the scanning drive unit 15 sequentially switches the lines L1 to Lx of the scanning line 5 for switching the voltage applied from the gate driver 15b between the on voltage and the off voltage, as shown in FIG. Then, reset processing Rm for one surface is performed, and reset processing for each radiation detection element 7 is performed while repeatedly performing reset processing Rm for one surface as necessary.

  In the present embodiment, the scanning drive unit 15 performs the reset process Rm for one surface only a predetermined number of times in the initial reset process of each radiation detection element 7. When is completed, an off voltage is applied from the gate driver 15b to all the lines L1 to Lx of the scanning line 5, and all the TFTs 8 of the sensor panel Sp are turned off.

  When the first reset process (Reset) of each radiation detection element 7 is completed, the control means 22 continues to leave the apparatus (D) and perform an offset correction value read process (E).

  Specifically, the control unit 22 first applies a turn-off voltage to all the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving unit 15 to turn off all the TFTs 8 in a later state. When radiation image capturing (A) is performed, all the TFTs 8 are left in the OFF state for the same amount of time as in the OFF state (D), and dark charges are accumulated in each radiation detection element 7. In this case, the radiation image capturing apparatus 1 is not irradiated with radiation.

  Subsequently, the control unit 22 transmits a signal instructing the offset correction value reading process to the scanning driving unit 15 as a trigger signal. Upon receiving this trigger signal, the scanning drive unit 15 sequentially switches the lines L1 to Lx of the scanning line 5 for switching the voltage applied from the gate driver 15b between the on voltage and the off voltage, as shown in FIG. Thus, the dark charges accumulated from the radiation detecting elements 7 connected to the lines L1 to Lx of the scanning line 5 through the TFTs 8 are released to the signal lines 6, respectively.

  Then, the control means 22 transmits a signal to the scanning drive means 15 and at the same time controls the readout circuit 17 to read out the dark charge emitted from each radiation detection element 7 as the offset correction value O, thereby offset correction value. A read process (E) is performed. The offset correction value O in this case is the same as the offset correction value O shown in FIG. The read offset correction value O for each radiation detection element 7 is stored in the storage unit 40.

  As can be seen by comparing the timing chart of various processes in continuous shooting and long shooting in the conventional case shown in FIG. 31 with the timing chart in the case of this embodiment shown in FIG. As described above, conventionally, the offset correction value read processing (E), which has been performed immediately after each radiographic image capturing, is performed before a series of radiographic image capturing in continuous imaging or long imaging.

  On the other hand, in the present embodiment, as shown in FIG. 15, the control unit 22 charges that remain in each radiation detection element 7 immediately after the offset correction value reading process (E) is performed as described above. Is read out as lag data Ld. A lag reading process (G1) is performed. The relationship between the lag data Ld and the offset Olag by the lag lag described above will be described later.

  In order to perform the lag reading process, the control unit 22 transmits a signal instructing the lag reading process to the scanning driving unit 15 as a trigger signal. In this embodiment, when the scanning drive unit 15 receives a signal instructing the lag reading process as a trigger signal, as shown in FIG. 16, the scanning driving unit 15 performs the gate at the same timing as in the immediately preceding offset correction value reading process. The lines L1 to Lx of the scanning line 5 for switching the voltage applied from the driver 15b between the on voltage and the off voltage are sequentially switched, and are connected to the lines L1 to Lx of the scanning line 5 through the TFTs 8. Charges remaining from the radiation detecting elements 7 are emitted to the signal lines 6 respectively.

  Then, the control unit 22 transmits a signal instructing the lag readout process to the scanning drive unit 15 and controls the readout circuit 17 so as to read out the remaining charge from each radiation detection element 7 as the lag data Ld. It has become. The read lag data Ld for each radiation detection element 7 is stored in the storage means 40.

  As shown in FIG. 16, the lag readout process (G1) is performed immediately after the offset correction value readout process (E) without charge accumulation or the like in each radiation detection element 7. That is, the offset correction value reading process (E) and the lag reading process (G1) are performed so that the reading process is performed twice in succession.

  However, it is also possible to perform a reset process for each radiation detection element 7 between the offset correction value reading process (E) and the lag reading process (G1) immediately after that. Thus, when comprised so that the reset process of each radiation detection element 7 may be performed, it is comprised so that the reset process Rm (refer FIG. 9) for one surface mentioned above may be performed about once.

  Further, in the case where the radiation detection element 7 is reset between the offset correction value readout process (E) and the lag readout process (G1) immediately after the offset correction value readout process (E), radiographic imaging described later is performed. The reset processing of each radiation detection element 7 performed between the offset correction value reading process and the lag reading process immediately after that is performed between the image reading process (B) for each time and the lag reading process (G) immediately after that. The radiation detection elements 7 are reset by the same processing method and timing.

  In the lag readout process (G1) immediately after the offset correction value readout process (E) before radiographic image capturing, normally, no charge due to the lag lag is accumulated in each radiation detection element 7. As shown in FIG. 17, the lag data Ld read in this case is obtained by reading the remainder of dark charges that could not be read out by the offset correction value reading process. Therefore, strictly speaking, the lag data Ld read in this case cannot be said to be caused by the lag lag.

  However, the lag data Ld read in the lag reading process (G1) immediately after the offset correction value reading process (E) is performed immediately after the image reading process (B) in each radiographic imaging, as will be described later. This is data serving as a reference (base) for performing subtraction processing from the lag data Ld read in the lag reading processing (G). Therefore, hereinafter, the lag data Ld read in the lag reading process (G1) immediately after the offset correction value reading process is referred to as reference lag data Ldbase in the sense of reference lag data.

  When the control means 22 finishes the lag readout process (G1) immediately after the offset correction value readout process (E), as shown in FIG. 15, the controller 22 repeats the reset process Rm for one surface in preparation for radiographic imaging. A reset process of each radiation detection element 7 (see the second “Reset” in the figure) is performed.

  At that time, a display unit such as a CRT (Cathode Ray Tube) or an LCD (Liquid Crystal Display) is provided on the console 57 (see FIG. 11) of the radiation generator 55, for example, an offset correction value reading process (E). When the lag readout process (G1) immediately after is completed, a ready signal is transmitted from the control means 22 of the sensor panel Sp to the radiation generator 55 via the communication means or the base station 54, and the ready signal is received. It is also possible to configure the radiation generating apparatus 55 to display the characters “READY” on the display unit of the console 57.

  An operator such as a radiologist finishes the alignment of the subject who is the subject Hu with the radiographic image capturing apparatus 1 or the long image capturing apparatus 100, moves from the imaging room R 1 to the front room R 2, and When the exposure switch 56 is operated and the button portion 56a of the exposure switch 56 is half-pressed (see FIG. 12B), an activation signal is transmitted from the exposure switch 56 to the radiation generator 55 via the console 57. The When receiving the activation signal, the radiation generation device 55 places the radiation source 52 in a standby state by starting rotation of the anode of the X-ray tube of the radiation source 52.

  Subsequently, as shown in FIG. 12C, when the operator fully presses the button portion 56a of the exposure switch 56, the radiation generator 55 starts irradiation from the exposure switch 56 via the console 57. A signal is transmitted. When the radiation generation device 55 receives the irradiation start signal from the exposure switch 56, the radiation generation device 55 transmits the irradiation start signal to the radiographic imaging device 1 or the long imaging device 100 via the base station 54 by a wireless method or a wired method. To do.

  When receiving the irradiation start signal from the radiation generator 55, the control means 22 of the radiographic imaging device 1 or the long imaging device 100 performs a reset process Rm for one surface at that time as shown in FIG. When the process is completed, an interlock release signal is transmitted to the radiation generator 55.

  Further, the control means 22 is in a state in which the off voltage is applied to all the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving means 15 when the reset process Rm for the last one surface is completed. All the TFTs 8 of the sensor panel Sp are held in an off state, and each radiation detection element 7 is shifted to a charge accumulation state in which charges generated therein are held. In this way, the first radiographic imaging (A) shown in FIG. 15 is started.

  When receiving the interlock release signal transmitted from the radiation imaging apparatus 1 or the long imaging apparatus 100 via the communication means or the base station 54, the radiation generation apparatus 55 emits radiation from the X-ray tube of the radiation source 52. Irradiate. Then, the radiation generator 55 irradiates the radiation from the radiation source 52 by, for example, stopping the X-ray tube of the radiation source 52 when a predetermined time has elapsed from the start of radiation irradiation from the radiation source 52. Stop.

  The control means 22 of the radiographic image capturing apparatus 1 or the long image capturing apparatus 100 irradiates the radiation from the radiation source 52 when a predetermined time has elapsed from the time when the interlock release signal is transmitted to the radiation generating apparatus 55. Is completed, the image reading process (B) is performed.

  In addition, it may be configured to transmit a signal indicating that the radiation has been terminated from the radiation generator 55 to the radiographic imaging apparatus 1 or the long imaging apparatus 100 when radiation irradiation from the radiation source 52 has been completed. The radiation image capturing apparatus 1 or the long image capturing apparatus 100 itself may be configured to detect the end of radiation irradiation.

  In the image reading process (B), the control unit 22 transmits a signal instructing the image reading process to the scanning driving unit 15 as a trigger signal. Further, when the scanning drive unit 15 receives this signal as a trigger signal, as shown in FIGS. 10 and 16, the gate driver 15b sequentially switches the lines L1 to Lx of the scanning line 5 while switching the on voltage and the off voltage. Apply. When the on-voltage is applied and the TFT 8 is turned on, the charges and the like generated in the respective radiation detection elements 7 are emitted from the respective radiation detection elements 7 to the respective signal lines 6 in accordance with the dose of the irradiated radiation. .

  Then, the control unit 22 transmits the signal to the scanning drive unit 15 and controls the readout circuit 17 to read out the electric charges emitted from each radiation detection element 7 as the image data d. The read image data d for each radiation detection element 7 is stored in the storage means 40.

  As shown in FIG. 15, when the image reading process (B) is performed, the control means 22 performs a lag reading process (G) for reading the lag data Ld from each radiation detection element 7 immediately after the image reading process (B). . The lag readout process in this case is performed with the same processing method and timing as the lag readout process (G1) immediately after the offset correction value readout process (E), as shown in FIG.

  In this case as well, the control means 22 transmits a signal instructing the lag readout process to the scanning drive means 15 and controls the readout circuit 17 so that the electric charge remaining from each radiation detection element 7 is used as the lag data Ld. It is designed to be read out. The read lag data Ld for each radiation detection element 7 is stored in the storage means 40.

  When the control means 22 finishes the lag readout process (G) immediately after the image readout process (B) as shown in FIG. 15, the control means 22 subsequently needs a reset process Rm for one surface as shown in FIG. This process is repeated as many times as necessary to reset the radiation detection elements (F).

  Further, in the case of long photographing using the long photographing apparatus 100, the control means 22 moves the moving mechanism control means 101b (see FIG. 5) during the reset processing (F) of each radiation detection element 7. 13 and FIG. 14) is instructed to activate the moving mechanism 101a to move the sensor panel Sp to the next position. The movement mechanism control unit 101b activates the movement mechanism 101a so that the sensor panel Sp moves to the next predetermined position in accordance with an instruction from the control unit 22.

  Further, in the case of continuous imaging using the radiographic image capturing apparatus 1, an operator such as a radiographer performs, for example, a radiographic image capturing apparatus for the body of the subject during the reset process (F) of each radiation detection element 7. Have the subject take the next pose, such as by changing the orientation relative to 1. In this case, in order to inform the operator that the pose of the subject may be changed, for example, the indicator 37 (see FIG. 1) of the radiographic image capturing apparatus 1 is turned on in a predetermined color, or the radiographic image capturing apparatus. It is possible to make a sound from 1.

  When a predetermined time has elapsed, an irradiation start signal is transmitted from the radiation generation device 55 to the radiographic imaging device 1 or the long imaging device 100 via the base station 54 (see FIG. 11). As shown in FIG. 18, at the time when the reset process Rm for one surface at that time is completed, an interlock release signal is transmitted to the radiation generator 55, and the last one surface When the reset process Rm is completed, the off-voltage is applied to all the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving unit 15 to charge each radiation detecting element 7 Transition to the accumulation state. In this way, the second radiographic image capturing (A) shown in FIG. 15 is started.

  Thereafter, as described above, the image readout process (B) after radiographic imaging (A), the lag readout process (G) immediately after that, and the reset process Rm for one surface are performed as many times as necessary. The reset process (F) of the radiation detection element is repeatedly performed.

  Therefore, when a series of continuous shooting or long shooting is completed, the storage unit 40 stores the offset correction value read by the offset correction value reading process (E) performed before the continuous shooting or long shooting. O, reference lag data Ldbase read in the lag readout process (G1) performed immediately after that, each image data d read out in the image readout process (B) for each radiographic imaging, and these The lag data Ld read out by the lag reading process (G) performed immediately after is stored as each data for each radiation detection element 7.

Next, a method for calculating true image data D ^* for each radiation detection element 7 in each radiographic image capturing performed in continuous imaging or long imaging using these data will be described.

The true image data D ^* may be calculated by the control means 22 of the radiographic image capturing apparatus 1 or the long image capturing apparatus 100, and each of these data is stored in the radiographic image capturing system. 50 (refer to FIG. 11, including the case where the radiographic imaging system 50 includes the long imaging apparatus 100) may be transmitted to the console 58 and performed by the console 58.

In the present embodiment, the control means 22 and the console 58, as shown in the following formula (3), are radiographic imaging (n = 1 to 3 in the above example) of continuous imaging and long imaging (in the above example, n = 1 to 3). A) The image data d (n) read in the subsequent image reading process (B) and the offset correction value O read in the offset correction value reading process (E) performed before the continuous shooting or the like. From the difference d (n) −O, the lag data Ld (n) read in the lag reading process (G) immediately after the image reading process (B) and the lag reading process immediately after the offset correction value reading process (E) The difference Ld (n) −Ldbase from the reference lag data Ldbase read in (G1) is subtracted, and the true image data D ^* (n) for each radiation detection element in the n-th radiographic imaging is obtained. Each is calculated.

D ^* (n) = d (n) -O- (Ld (n) -Ldbase) (3)
Hereinafter, the reason why the present embodiment is configured to calculate the true image data D ^* (n) by performing the above calculation will be specifically described.

  As can be seen from the characteristics of the lag lag described above, when a series of radiographic imaging (A) is repeatedly performed in continuous imaging or long imaging as described above, image readout processing after the second radiographic imaging (B The lag data Ld (2) resulting from the lag lag generated in the first radiographic image capturing is superimposed on the image data d (2) read out in (1). Further, the image data d (3) read out in the image reading process (B) after the third radiographic image capturing is caused by each lag lag generated in each of the first and second radiographic image capturing. The lag data Ld (3) is superimposed.

  Further, an offset correction value O corresponding to the dark charge accumulated while the TFT 8 is in the OFF state at the time of radiographic image capturing (A) is superimposed on each image data d (n).

Based on these points, the true image data D ^* () from the image data d (n) read out in the image reading process (B) after the n-th radiographic imaging (A) in continuous imaging or long imaging. A method for calculating n) will be described with reference to FIG.

  As described above, the image data d (n) read out in the image reading process (B) after the n-th radiographic imaging (A) includes the offset correction value O caused by the dark charge and before that. The offset amount Olag (n) due to the lag lag generated in the radiographic image capturing performed in FIG.

Therefore, the image data d (n), the offset correction value O, the offset amount Olag (n) caused by the lag lag, and the true value generated in each radiation detection element 7 due to radiation irradiation in the radiographic imaging. The relationship with the image data d ^* (n) of
d (n) = d ^* (n) + O + Olag (n)
∴d ^* (n) = d (n) −O−Olag (n) (4)
It becomes.

  On the other hand, the lag readout process (G) immediately after the n-th image readout process (B) is performed in the same manner and timing as the lag readout process (G1) immediately after the offset correction value readout process (E). 19, the lag data Ld (n) read in the lag reading process (G) immediately after the n-th image reading process (B) includes the lag reading process (G1 immediately after the offset correction value reading process). The reference lag data Ldbase (see FIG. 17) read in

  Also, as shown in FIG. 16, during the lag readout process, the on-voltage is applied to each of the lines L1 to Lx of the scanning line 5 for the same time as the image readout process. At the time of reading the lag data Ld (n) in the lag reading process (G) immediately after the n-th image reading process (B), each radiation detection element 7 performs each of the n-th image reading process (B). The same offset amount Olag (n) as the offset amount Olag (n) caused by the lag lag read from the radiation detection element 7 is read.

  Further, the lag data Ld (n) read in the lag reading process (G) immediately after the n-th image reading process is left unread in the immediately preceding image reading process (B), that is, from each radiation detection element 7. Data Δd (n) resulting from the charge remaining in each radiation detection element 7 without being completely read out is also included.

Therefore, the lag data Ld (n), the reference lag data Ldbase, the offset Olag (n) due to the lag lag, and the data Δd (n) due to the unread charges in the image reading process (B).
The relationship with
Ld (n) = Δd (n) + Ldbase + Olag (n) (5)
It becomes.

When the above equation (5) is transformed,
Olag (n) = Ld (n) −Δd (n) −Ldbase (6)
And substituting this into Olag (n) in equation (4) above,
d ^* (n) = d (n) −O− (Ld (n) −Δd (n) −Ldbase)
∴d ^* (n) −Δd (n) = d (n) −O− (Ld (n) −Ldbase) (7)
It becomes.

Then, when d ^* (n) −Δd (n) in the above equation (7) is set to D ^* (n), the above equation (3) is obtained.

A part of the data Δd (n) resulting from the unread charges in the image reading process (B) remains as the above-mentioned lag lag, but according to the study by the present inventors, this data The size of the data Δd (n) itself due to the unread charges in the image reading process (B) is generated in each radiation detection element 7 by the irradiation of the radiation image and is read out in the image reading process. It has been found that it is proportional to the size of the true image data d ^* (n) to be performed.

That is, if the proportionality constant is α,
Δd (n) = α × d ^* (n) (8)
And D ^* (n) is
D ^* (n) = d ^* (n) −Δd (n)
∴D ^* (n) = (1−α) × d ^* (n) (9)
The relationship holds.

Therefore, the above D ^* (n) is (1−α) × 100 of the true image data d ^* (n) generated in each radiation detection element 7 due to radiation irradiation in radiographic imaging. % Value. Therefore, strictly speaking, this D ^* (n) is not the true image data d ^* (n) itself generated in each radiation detection element 7 due to radiation irradiation, but is a value proportional thereto. In a sense, in the present invention, D ^* (n) is referred to as true image data D ^* (n).

Thus, in this embodiment, as described above, the control means 22 and the console 58 of the radiographic image capturing apparatus 1 and the long image capturing apparatus 100 and the console 58 perform a series of radiographic image capturing in continuous image capturing and long image capturing. The offset correction value O read in the offset correction value reading process (B) performed in step S1, the reference lag data Ldbase read in the lag read process (G1) immediately after the offset correction value read process, Image data d (n) (n = 1 to 3 in the above example) read in the image reading process (B) after each radiographic imaging (A) in long imaging, and image reading from lug data Ld (n) read in the lugs reading process immediately after the process (G), according to the above (3), respectively calculated true image data D ^* a ⁽ⁿ⁾ for each radiation detection element 7 It has become the jar.

Note that, for example, the above-described proportionality constant α is obtained in advance through experiments or the like, and D ^* (n) calculated according to the above equation (3) is divided by (1−α) to obtain a true true value. It may be configured to calculate the image data d ^* (n).

  On the other hand, when configured as described above, as shown in FIG. 15, as a control configuration of each process in each radiographic image capturing at the time of continuous imaging or long imaging, radiographic imaging (A) and one surface It is only necessary to perform the readout process (B), the lag readout process (G) for one surface, and the reset process (F) of each radiation detection element 7 for performing the reset processing Rm for one surface as many times as necessary.

  Then, as can be seen by comparing this with the control configuration of each processing in each radiographic imaging at the time of continuous imaging or long imaging in the conventional method shown in FIG. The interval between imaging, that is, the time required from the start of the n-th radiographic imaging to the start of the next n + 1 radiographic imaging is each radiographic image for offset correction value readout processing in the conventional method The time is shorter than the conventional method because the resetting process (C) of the imaging apparatus and the leaving of the apparatus (D) (see FIG. 31) with the TFT turned off for the same time as the radiographic imaging are not performed. .

  Since the interval between each radiographic image capturing is shortened in this way, in this embodiment, as shown in FIG. 20, the time required for continuous imaging and long imaging in which a series of radiographic image capturing is repeated is shortened. The time T during which the subject who is the subject must be restrained in a state where the subject cannot be separated from the radiographic imaging apparatus at least from the first radiographic imaging to the final radiographic imaging is shorter than that in the case of the conventional method. Become. Therefore, it is possible to reduce the burden on the subject.

  As described above, according to the radiation image capturing apparatus 1 and the radiation image capturing system 50 including the long image capturing apparatus 100 according to the present embodiment, before the series of radiographic image capturing of continuous image capturing or long image capturing, An offset correction value reading process (E) (see FIG. 15 and FIG. 20) is performed, which is left for a predetermined time in a state where no radiation is irradiated, and reads the charge accumulated in each radiation detection element 7 as an offset correction value O. Immediately thereafter, a lag reading process (G1) for reading the reference lag data Ldbase is performed.

  Then, in a series of radiographic imaging such as continuous imaging and long imaging, every time radiographic imaging is performed, the charge accumulated in each radiation detection element 7 according to the dose of the irradiated radiation is image data d. The image readout process (B) to be read as (n) and the lag readout process (G) immediately after that are performed. At this time, the offset correction value readout process (E) before radiographic image capturing and the lag readout process immediately after that are performed. The image reading process (B) and the lag reading process (G) immediately after that are performed at the same processing method and timing as in (G1).

  With this configuration, in each radiographic imaging in continuous imaging or long imaging, a lag lag occurs in radiographic imaging before that, and even if the reset processing of each radiation detecting element 7 is repeated during each radiographic imaging. Even when the lag lag cannot be completely removed and the offset Olag (n) due to the lag lag generated in the previous radiographic image capturing is included in the image data d (n), the lag readout process By using the read lag data Ld (n) and the reference lag data Ldbase, it is possible to accurately eliminate the offset Olag (n) due to the lag lag from the image data d (n).

Then, after accurately eliminating the offset amount Olag (n) due to the lag lag from the image data d (n), the offset correction value O read out by the offset correction value reading process is further subtracted, whereby each radiation The true image data D ^* (n) for each detection element 7 can be accurately calculated.

  In addition, according to the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 including the long image capturing apparatus 100 according to the present embodiment, the offset correction value is read every time radiographic image capturing is performed, as in the conventional method (see FIG. 31). It is not necessary to perform reset processing (C) of each radiographic image capturing apparatus for processing or leaving the apparatus (D) in a state where the TFT is turned off for the same time as radiographic image capturing. It is possible to shorten the interval between them, and it is possible to reduce the time required for continuous imaging and long imaging in which a series of radiographic imaging is repeated.

  Therefore, the time T during which the subject who is the subject must be restrained in a state in which the subject cannot be separated from the radiographic imaging apparatus at least from the first radiographic imaging to the final radiographic imaging is set as compared with the conventional method. It becomes possible to shorten and to reduce the burden placed on the subject.

  Specifically, in the conventional case shown in FIG. 31, for example, radiographic imaging (A) is 1 second, image readout processing (B) is 0.5 seconds, and each radiation detection element 7 is reset (C). If it takes 1 second to leave, 1 second to stand (D), 0.5 second to read the offset correction value (E), and 3 seconds to reset (F) (and move) each radiation detection element thereafter, The time T for restraining is a total of 15 seconds of (1 + 0.5 + 1 + 1 + 0.5 + 3) × 2 + 1.

  On the other hand, for example, in the radiographic image capturing apparatus 1 and the radiographic image capturing system 50 including the long image capturing apparatus 100 according to the present embodiment illustrated in FIG. 20, the image reading process (B) takes 1 second for radiographic image capturing (A). , 0.5 seconds for the lag readout process (G), and 3 seconds for the subsequent reset process (F) (and movement) of each radiation detection element, the time T for restraining the subject is ( 1 + 0.5 + 0.5 + 3) × 2 + 1 total 11 seconds, and the time T for restraining the subject can be shortened.

As can be seen by comparing the above equation (1) and the above equation (3) according to the present invention, in the first and second embodiments, a true image for each radiation detection element 7 is obtained. In order to obtain the data D ^* (n), it is necessary to further subtract the two components of the offset correction value O and the difference Ld (n) −Ldbase from the image data d (n). The offset correction value O and the difference Ld (n) −Ldbase include image noises that are not correlated with each other due to each electrical noise. Therefore, in this way, by subtracting the offset correction value O and the difference Ld (n) −Ldbase twice from the image data d (n), it is superimposed on the calculated true image data D ^* (n). Noise may increase.

Since the difference Ld (n) −Ldbase related to the lag is related to the lag generated in the radiographic imaging performed before the radiographic imaging for calculating the true image data D ^* (n), The value of the difference Ld (n) −Ldbase is not necessarily calculated strictly for the image data d (n) of all the radiation detection elements 7.

  Therefore, the control means 22 and the console 58 of the radiographic image capturing apparatus 1 and the long image capturing apparatus 100 and the lag data Ld (n) read by the lag read processing (G1, G) and the reference lag as described above. When performing the subtraction process with the data Ldbase, it is possible to perform the subtraction process by performing a smoothing process on the calculated difference Ld (n) −Ldbase.

  As the smoothing process, as is well known in the field of image processing or the like, for example, a total of nine radiation detection elements 7 including the radiation detection element 7 and eight radiation detection elements 7 adjacent to the periphery thereof. The difference Ld (n) −Ldbase can be performed by applying various 3 × 3 smoothing filters, and high frequency components are removed by general spatial filter processing or the like. It is also possible to configure.

And if comprised in this way, when calculating the true image data D ^* (n) for each radiation detection element 7 using the above equation (3), it is superimposed on the true image data D ^* (n). Noise can be reduced, and the image quality of the radiation image generated based on the true image data D ^* (n) for each radiation detection element 7 with reduced noise can be further improved. Become.

[Second Embodiment]
In the second embodiment of the present invention, the lag readout process (G) (see FIGS. 15 and 20) in a series of radiographic image capturing of continuous imaging and long imaging is performed in a shorter time than in the case of the first embodiment. By performing the above, the interval between each radiographic image capturing can be further shortened, and the radiographic image capturing apparatus 1 or the long one that can further shorten the time required for continuous imaging or long imaging in which a series of radiographic image capturing is repeated. The scale photographing apparatus 100 and the radiation image photographing system 50 will be described.

  Also in the present embodiment, the configurations of the radiographic image capturing apparatus 1, the long image capturing apparatus 100, and the radiographic image capturing system 50 are the same as those in the first embodiment, and the same functional units as those in the first embodiment. Are described with the same reference numerals.

  In the present embodiment, as described above, the method of the lag readout process (G) for each radiographic image capture in the control configuration of each process during continuous imaging or long imaging is different from that in the first embodiment.

  In addition, as described in the first embodiment, the image reading process (B) for each radiographic image capturing and the lag reading process (G) immediately after the radiation reading process are the same as the offset correction value reading process (E) and the lag immediately thereafter. Since it is configured to perform the same processing method and timing as the reading process (G1), as described above, when changing the method of the lag reading process (G) for each radiographic image capturing, the offset correction value reading is performed. The method of the lag reading process (G1) performed immediately after the process is similarly changed.

  In addition, between the image readout process (B) for each radiographic image capture and the lag readout process (G) immediately after that, or between the offset correction value readout process (E) and the lag readout process (G1) immediately after that. As in the case of the first embodiment, the radiation detection elements 7 can be configured to be reset.

  In the present embodiment, in the lag readout process (G, G1) performed immediately after the image readout process (B) or immediately after the offset correction value readout process (E), the process of the first embodiment shown in FIG. Unlike the case, as shown in FIG. 21, the gate driver 15b of the scanning drive unit 15 applies a predetermined number (β) of lines L of the scanning lines 5 as a set, and simultaneously applies an ON voltage for each set. Configured to do. Then, a lag readout process is performed by applying an on-voltage to the lines L of all the scanning lines 5 while sequentially switching a set of a predetermined number of scanning lines. Hereinafter, a case where the predetermined number (β) of the scanning lines 5 preset as a set of units is four (that is, β = 4) will be described, but the predetermined number is not limited to four. .

  If comprised in this way, as shown in FIG. 22, each radiation detection element 7n-7n respectively connected via TFT8 to the line Ln-Ln + 3 of the said predetermined number of scanning lines 5 to which ON voltage was applied. +3, the charges qn to qn + 3 remaining in the respective radiation detection elements 7n to 7n + 3 are simultaneously discharged to one signal line 6, and each radiation detection element 7n is supplied to the capacitor 18b of the amplifier circuit 18. A total value qn + qn + 1 + qn + 2 + qn + 3 of charges qn to qn + 3 released from .about.7n + 3 is accumulated.

  As described above, the operational amplifier of the amplifier circuit 18 outputs a voltage value corresponding to the amount of charge accumulated in the capacitor 18b. In this case, the charge discharged from each of the radiation detection elements 7n to 7n + 3. A voltage value corresponding to the total value qn + qn + 1 + qn + 2 + qn + 3 of qn to qn + 3 is output from the amplifier circuit 18, and the voltage value is the value of the lag readout process (G) immediately after the image readout process (B). In this case, it is read as lag data Ld (n), and in the case of the lag reading process (G1) immediately after the offset correction value reading process (E), it is read as the reference lag data Ldbase.

  In addition, when the amplifier circuit 18 has a binning mode (bin mode), that is, the charges emitted from the plurality of radiation detection elements 7 connected to the plurality of signal lines 6 are collected into one signal line 6 and In the case where the amplifier circuit 18 connected to one signal line 6 is configured to be able to perform charge-voltage conversion. In such a case, for example, as shown in FIG. 23, the lines Ln to Ln + 3 of the predetermined number of scanning lines 5 to which the on-voltage is applied are connected via the TFTs 8 respectively. Total value qnA + qn of charges qnA to qn + 3A and qnB to qn + 3B emitted from the radiation detection elements 7nA to 7n + 3A and the radiation detection elements 7nB to 7n + 3B connected to the adjacent signal lines 6, respectively. + 1A + qn + 2A + qn + 3A + qnB + qn + 1B + qn + 2B + qn + 3B is accumulated.

  In this case, the voltage value corresponding to the total value of the charges qnA to qn + 3A and qnB to qn + 3B emitted from the radiation detection elements 7nA to 7n + 3A and 7nB to 7n + 3B is the amplification circuit 18. In the case of the lag readout process (G) immediately after the image readout process (B), the voltage value is read out as lag data Ld (n) and immediately after the offset correction value readout process (E). In the case of the lag reading process (G1), the data is read as the reference lag data Ldbase.

  In FIG. 23, the case of the binning mode in which the charges from the radiation detection elements 7 connected to the two signal lines 6 are combined into one signal line 6 is shown. The number (γ) of signal lines 6 to be combined into one signal line 6 is not limited to two, and can be set to an arbitrary number that can be set by the reading IC 16. Is possible.

  When configured as described above, in the first embodiment, as shown in FIG. 16, lag reading is performed while applying an on-voltage to each line L of the scanning lines 5 from the gate driver 15 b of the scanning driving unit 15. Although the processing (G1, G) is performed, in this embodiment, as shown in FIG. 21, the lag readout processing (while the on-voltage is simultaneously applied to the predetermined number (β) of lines L of the scanning lines 5 ( In order to perform G1, G), as shown in FIG. 24, the time required for the lag readout process (G1, G) is 1 / β in the first embodiment (β is four as described above). In this case, it can be shortened to 1/4).

  Therefore, it is possible to further shorten the interval between each radiographic image capturing in continuous imaging or long imaging, compared to the first embodiment, and the time required for continuous imaging or long imaging in which a series of radiographic image capturing is repeated. Can be shortened. Therefore, in the case of the first embodiment, the time T in which the subject who is the subject must be restrained in a state in which the subject cannot be separated from the radiographic imaging apparatus at least from the first radiographic imaging to the final radiographic imaging. It is possible to further reduce the burden on the subject.

By the way, in the case of such a configuration, the reference lag data Ldbase and lag data Ld (n) read in the lag reading process (G1, G) are the charges read from the β radiation detecting elements 7, or In the case of using the binning mode, since the data corresponds to the charges read from the radiation detecting elements 7 corresponding to β × γ, the data is directly substituted into the above equation (3) and true for each radiation detecting element 7. Cannot be used to calculate the image data D ^* (n).

  Therefore, the control means 22 and the console 58 of the radiographic image capturing apparatus 1 and the long image capturing apparatus 100 and the console 58 read the lag data Ld (n) read out in the lag reading process (G1) as described above by 1 / β times. To do. For example, as shown on the left side of FIG. 25, the same Ld (n) / β (“5” and “1” in the figure) is applied to each of β radiation detection elements 7 arranged in the direction of the signal line 6 (vertical direction in the drawing). For example, interpolation processing such as linear interpolation is performed on Ld (n) / β between β radiation detection elements 7 adjacent in the direction of the signal line 6. Then, as shown on the right side of FIG. 25, the lag data Ld (n) for each radiation detection element 7 is calculated.

  This process is performed for the reference lag data Ldbase read in the lag reading process (G1) in the same manner, and the reference lag data Ldbase for each radiation detection element 7 is calculated. Further, when the binning mode is used, the reference lag data Ldbase and the lag data Ld (n) are multiplied by 1 / (β × γ) and the illustration is omitted. The reference lag data Ldbase for each radiation detection element 7 is calculated by performing interpolation processing such as linear interpolation in the direction of line 5 (lateral direction in FIG. 25), for example.

Then, the control means 22 and the console 58 of the radiographic imaging device 1 and the long imaging device 100 use the lag data Ld (n) and the reference lag data Ldbase calculated for each radiation detection element 7 as described above ( 3) Substituting into the equation, true image data D ^* (n) for each radiation detection element 7 is calculated.

  With this configuration, the time T for restraining the subject can be further shortened as described above, and β (or β × γ in the binning mode) charge from each radiation detection element 7 is obtained. Therefore, even if there is fluctuation in the reference lag data Ldbase and lag data Ld (n) read out from the individual radiation detection elements 7 by the lag readout processing (G1, G), By adding them, reference lag data Ldbase and lag data Ld (n) can be obtained in a state where fluctuations of individual data are canceled out. Therefore, there is an effect that it is possible to calculate the reference lag data Ldbase and lag data Ld (n) for each radiation detection element 7 in a state where fluctuations are offset and reduced.

  On the other hand, in the lag readout process (G1, G), for example, as shown in FIG. 26, the scanning line is selected from the gate line 15b of the scanning driving means 15 by, for example, every third line L1 of the scanning line 5. It is also possible to apply a turn-on voltage to the scanning line 5 selected in advance so that predetermined thinning is performed by selecting a part of all the five lines L. Note that the present invention is not limited to the case where every third scanning line 5 is selected in advance.

  Also with this configuration, as shown in FIG. 24, the time required for the lag readout process (G1, G) can be further shortened compared to the case of the first embodiment. Therefore, the time T for restraining the subject can be made shorter than in the case of the first embodiment, and the burden on the subject can be reduced.

  In this case, unlike the above example, the reference lag data Ldbase and lag data Ld (n) read in the lag reading process (G1, G) are the reference lag data Ldbase and lag read from the individual radiation detection elements 7. Since the data is Ld (n), it is not necessary to multiply by 1 / β as described above. When the binning mode is used, it is necessary to multiply the reference lag data Ldbase and lag data Ld (n) read by the lag reading process (G1, G) by 1 / γ.

  The control means 22 and the console 58 of the radiographic image capturing apparatus 1 and the long image capturing apparatus 100 and the console 58 read the reference lag data Ldbase and lag data Ld () read by the lag reading process (G1, G) as described above. Although not shown based on n), the reference lag data Ldbase and the lag data Ld (n) for each radiation detection element 7 are calculated by performing interpolation processing such as linear interpolation, for example. Composed.

Then, the lag data Ld (n) and the reference lag data Ldbase for each radiation detection element 7 calculated in this way are substituted into the above equation (3), and the true image data D ^* for each radiation detection element 7 is obtained ^. It is configured to calculate (n).

  With this configuration, the time T for restraining the subject can be further shortened as described above, and the number of scanning lines 5 to which the on-voltage is applied in the lag readout process (G1, G) is reduced. There is also an effect that it is possible to reduce power consumption in the radiographic image capturing apparatus 1 and the long image capturing apparatus 100.

  As another method, for example, as shown in FIG. 27, in the lag readout process (G1, G), the on-voltage is applied to the lines L1 to Lx of the scanning line 5 from the gate line 15b of the scanning driving unit 15. The lag readout process (G1) is applied such that the application time is changed to be shorter than the offset correction value readout process (E) and the image readout process (B). , G) can also be configured.

  In this case, the on-time in the lag readout process (G) immediately thereafter is shorter than the on-time in the image readout process (B) shown in FIG. 19 (the time from “TFTon” to “TFToff” in the figure). Therefore, the offset Olag (n) by the lag lag included in the image data d (n) read in the image reading process (B) and the lag data Ld (n) read in the lag reading process (G) immediately after that are included in the image data d (n). The offset Olag (n) due to the included lag lag has a different value, and Olag (n) calculated by the above equation (6) is substituted into Olag (n) of the above equation (4). (3) The equation cannot be obtained.

  Further, the offset Olag (n) due to the lag lag contained in the lag data Ld (n) does not necessarily increase or decrease in proportion to the on-time. Therefore, when the lag readout process (G1, G) is performed by varying the on-time as described above, the on-time for the offset Olag (n) by the lag lag before the on-time is varied is set. The change rate δ of the offset Olag (n) due to the lag lag after being varied is obtained in advance by experiments or the like.

The control means 22 and the console 58 of the radiographic image capturing apparatus 1 and the long image capturing apparatus 100 and the console 58 are obtained by the lag readout processing (G1, G) performed by varying the on-time so as to shorten as described above. The obtained reference lag data Ldbase and lag data Ld (n) are multiplied by 1 / δ and substituted into the above equation (3) to calculate the true image data D ^* (n) for each radiation detecting element 7. Configured.

  Also with this configuration, as shown in FIG. 24, the time required for the lag readout process (G1, G) can be further shortened compared to the case of the first embodiment. Therefore, the time T for restraining the subject can be made shorter than in the case of the first embodiment, and the burden on the subject can be reduced.

  Various modifications to the first embodiment shown in the second embodiment can be combined with each other.

  In the first and second embodiments described above, the case of performing radiographic imaging three times in continuous imaging or long imaging has been described. However, the present invention is not limited to the case where radiographic imaging is performed three times. Needless to say, the present invention can be applied to a case where radiographic imaging is appropriately performed a plurality of times in continuous imaging or long imaging.

DESCRIPTION OF SYMBOLS 1 Radiographic imaging device 5, L1-Lx Scan line 6 Signal line 7 Radiation detection element 8 TFT (switch means)
DESCRIPTION OF SYMBOLS 15 Scanning drive means 17 Reading circuit 22 Control means 39 Antenna apparatus (communication means)
DESCRIPTION OF SYMBOLS 50 Radiation imaging system 52 Radiation source 55 Radiation generator 58 Console 100 Long imaging | photography apparatus (radiation imaging apparatus)
101 Moving means A Radiographic imaging B Image readout process D Leaving d, d (n) Image data D ^* (n) True image data E Offset correction value readout process G Lag readout process immediately after image readout process G1 Offset correction value readout Lag readout processing immediately after processing Hu Subject Ld, Ld (n) Lag data Ldbase Reference lag data (lag data)
O Offset correction value q Charge r Region Rm Reset processing for one surface (reset processing of each radiation detection element)
Sp sensor panel β Predetermined number of scanning lines

Claims (12)

A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; ,
A readout circuit that reads out charges accumulated in each of the radiation detection elements through the signal lines;
An off state and an on state are switched according to a voltage applied to the connected scanning line, arranged for each radiation detection element, and in the off state, the charge generated in the radiation detection element is retained, Switch means for releasing the charge from the radiation detection element in the ON state;
Scanning drive means for switching a voltage applied to the switch means via the scanning line between an on voltage and an off voltage;
Control means for controlling at least the readout circuit and the scanning drive means to perform readout processing of the charges from the radiation detection elements;
With
The control means reads out the offset correction value read out as an offset correction value after storing the radiation detecting element in a state where the radiation detecting element is not irradiated with radiation for a predetermined time before radiographic imaging. Immediately after the processing is performed, a lag readout process for reading out the electric charge remaining in each of the radiation detection elements as lag data is performed, and each time radiographic imaging is performed, depending on the dose of irradiated radiation. The image reading process for reading out the electric charge accumulated in each of the radiation detection elements as image data and the lag reading process immediately after that are performed in the same manner and timing as the offset correction value reading process and the lag reading process immediately after that. The radiographic imaging device characterized in that each of them is performed. A plurality of scanning lines and a plurality of signal lines arranged so as to intersect with each other; a plurality of radiation detecting elements arranged in a two-dimensional manner in each region partitioned by the plurality of scanning lines and the plurality of signal lines; ,
A readout circuit that reads out charges accumulated in each of the radiation detection elements through the signal lines;
An off state and an on state are switched according to a voltage applied to the connected scanning line, arranged for each radiation detection element, and in the off state, the charge generated in the radiation detection element is retained, Switch means for releasing the charge from the radiation detection element in the ON state;
Scanning drive means for switching a voltage applied to the switch means via the scanning line between an on voltage and an off voltage;
Control means for controlling at least the readout circuit and the scanning drive means to perform readout processing of the charges from the radiation detection elements;
A sensor panel comprising:
Moving means for relatively displacing the positional relationship between the sensor panel and the subject;
With
The control means reads out the offset correction value read out as an offset correction value after storing the radiation detecting element in a state where the radiation detecting element is not irradiated with radiation for a predetermined time before radiographic imaging. Immediately after the processing is performed, a lag readout process for reading out the electric charge remaining in each of the radiation detection elements as lag data is performed, and then the relative positional relationship between the sensor panel and the subject is determined by the moving means. Each time a radiographic image is taken while being displaced, an image readout process for reading out the electric charge accumulated in each of the radiation detection elements as image data in accordance with the dose of the irradiated radiation, and a lag readout process immediately after that, The same processing method and timing as the offset correction value reading process and the lag reading process immediately after the offset correction value reading process Radiographic imaging apparatus characterized by performing, respectively.   The control means performs a reset process for releasing the remaining charges from the radiation detection elements between the offset correction value readout process and the lag readout process immediately after the offset correction value readout process, and the image readout process for each radiographic image capture. Even during the lag readout process immediately after that, each of the radiation detection elements in the same manner and timing as the reset process of each radiation detection element performed between the offset correction value readout process and the lag readout process immediately after that. The radiation image capturing apparatus according to claim 1, wherein a reset process of the radiation detection element is performed.   The control means determines the difference between the image data read in the image read process and the offset correction value read in the offset correction value read process in the lag read process immediately after the image read process. Subtracting the difference between the read lag data and the lag data read in the lag read process immediately after the offset correction value read process, the true image data for each radiation detection element The radiation image capturing apparatus according to claim 1, wherein the radiation image capturing apparatus calculates the radiation image capturing apparatus.   The control unit applies the on-voltage with a predetermined number of the scanning lines set in advance from the scan driving unit in the lag readout process immediately after the offset correction value readout process as a set via the switch unit. Then, a total value of charges remaining in each radiation detection element is read from each radiation detection element connected to the predetermined number of scanning lines as lag data, and the on-voltage is applied from the scanning drive means The lag readout process is performed while sequentially switching the set of the predetermined number of scanning lines, and the lag readout process immediately after the image readout process performed for each radiographic image capturing is replaced by the lag immediately after the offset correction value readout process. 4. The method according to claim 1, wherein the same processing method and timing as the reading processing are performed. Radiographic imaging apparatus according to an item.   The control means applies the on-voltage to the scanning line preselected from the scanning driving means in the lag readout processing immediately after the offset correction value readout processing, and connects to the scanning line via the switch means. The lag readout process is performed by sequentially reading out the charge remaining in each radiation detection element from each of the radiation detection elements as lag data, and sequentially switching the scanning lines to which the on-voltage is applied from the scanning drive means. And performing the lag readout process immediately after the image readout process performed for each radiographic image capturing in the same manner and timing as the lag readout process immediately after the offset correction value readout process. The radiographic imaging apparatus as described in any one of Claims 1-3.   The control means applies the ON voltage from the scanning drive means to the switch means via the scanning line in each of the lag reading processes performed immediately after the offset correction value reading process and immediately after the image reading process. Each of the lag readout processes is made variable so that the time is shorter than the time during which the on-voltage is applied to the switch means from the scanning drive means via the scanning line in the offset correction value readout process and the image readout process. The radiographic imaging apparatus according to any one of claims 1 to 3, 5, and 6, wherein:   The control means calculates lag data for each radiation detection element based on the lag data read in each lag readout process or a total value of the charges read out as the lag data, and the image readout process Based on the difference between the read image data and the offset correction value read in the offset correction value read process, based on the lag data read in the lag read process immediately after the image read process Difference between the calculated lag data for each radiation detection element and the lag data for each radiation detection element calculated based on the lag data read in the lag readout process immediately after the offset correction value readout process To calculate true image data for each of the radiation detection elements. Radiographic imaging apparatus according to any one of claims 7 from claim 5.   The control means includes the lag data and the offset correction value for each radiation detection element calculated based on the lag data read out in the lag readout process immediately after the image readout process during the subtraction process. Performing a subtraction process by performing a smoothing process on a difference from the lag data for each of the radiation detection elements calculated based on the lag data read out in the lag readout process immediately after the readout process. 9. The radiographic image capturing apparatus according to claim 4, wherein the radiographic image capturing apparatus is characterized. The radiographic imaging apparatus according to any one of claims 1 to 3, further comprising a communication unit capable of transmitting and receiving information;
A radiation generator comprising a radiation source for irradiating the radiation imaging apparatus with radiation;
The image data read from the image reading process, the offset correction value read by the offset correction value reading process, and the lag reading immediately after the image reading process transmitted from the radiation image capturing apparatus Based on the lag data read in the process and the lag data read in the lag read process immediately after the offset correction value read process, the difference between the image data and the offset correction value, A console for calculating true image data for each radiation detection element by subtracting the difference between the lag data read in the lag readout process immediately after the image readout process and the offset correction value readout process. When,
A radiographic imaging system comprising: The radiographic imaging apparatus according to any one of claims 5 to 7, further comprising a communication unit capable of transmitting and receiving information;
A radiation generator comprising a radiation source for irradiating the radiation imaging apparatus with radiation;
The image data read from the image reading process, the offset correction value read by the offset correction value reading process, and the lag reading immediately after the image reading process transmitted from the radiation image capturing apparatus The lag data or the lag data read by the lag read process based on the lag data read by the process and the lag data read by the lag read process immediately after the offset correction value read process The lag data for each of the radiation detection elements is calculated based on the total value of the charges read out as the image data read out in the image reading process and the offset read out in the offset correction value reading process. From the difference from the correction value, the lag reading immediately after the image reading process is performed. Calculated based on the lag data for each of the radiation detection elements calculated based on the lag data read out in the processing, and the lag data read out in the lag readout processing immediately after the offset correction value readout processing A console for subtracting the difference from the lag data for each radiation detection element and calculating true image data for each radiation detection element;
A radiographic imaging system comprising:   The console reads out the lag data and the offset correction value for each radiation detection element calculated based on the lag data read out in the lag readout process immediately after the image readout process during the subtraction process. A smoothing process is performed on a difference from the lag data for each of the radiation detection elements calculated based on the lag data read out in the lag reading process immediately after the process, and the subtraction process is performed. The radiographic imaging system according to claim 10 or 11.