JP2019128242A - Radiation imaging apparatus and control method thereof, as well as radiation imaging system - Google Patents

Abstract

To provide a mechanism in which preferred correction of a crosstalk component can be performed for a detection signal for monitoring irradiation with radiation.SOLUTION: A radiation imaging apparatus comprises: a radiation detection unit 113 that is constituted to include a detection pixel 1131 for performing at least either one detection of detection of an irradiation start of radiation, detection of an irradiation stop of the radiation, and detection of an accumulated irradiation amount of the radiation; and an imaging apparatus control unit 118 that switches between a first correction method in which a first output signal being an output signal of the detection pixel 1131 when a first switch 11312 of the detection pixel 1131 is in a conductive state is corrected using a second output signal being the output signal of the detection pixel 1131 when the first switch 11312 of the detection pixel 1131 is in a non-conductive state, and a second correction method in which the first output signal is corrected using other output signal being different from the second output signal, to select.SELECTED DRAWING: Figure 2

Description

  The present invention relates to a radiation imaging apparatus that performs imaging (imaging) using radiation, a control method thereof, and a radiation imaging system.

  Radiation imaging apparatuses using sensor panels that detect radiation such as X-rays are widely used in fields such as industry and medicine. In recent years, multi-functionalization of this radiation imaging apparatus has been studied. As one of the functions, a radiation imaging apparatus having a function of monitoring radiation irradiation has been considered. The function of monitoring radiation irradiation enables, for example, detection of timing when radiation irradiation from a radiation source is started, detection of timing when radiation irradiation should be stopped, detection of radiation dose and integrated dose It becomes. In addition, the automatic exposure control (Automatic Exposure Control) is performed by detecting the cumulative dose of radiation that has passed through the subject and stopping the radiation irradiation by the radiation source when the detected cumulative dose reaches an appropriate amount. AEC) will also be possible.

  In such a radiation imaging apparatus, a parasitic capacitance that can not be ignored exists between an electrode of a pixel that detects radiation and a signal line connected to the pixel. Then, through this parasitic capacitance, crosstalk may occur in which the potential variation of the electrode of the pixel caused by the radiation irradiation is transmitted to the signal line connected to the pixel. A signal flowing through a signal line connected to a pixel includes a signal component from the pixel and a component generated by crosstalk. Due to this cross-talk component, it is difficult to accurately obtain the signal from the pixel during radiation irradiation. Then, when the signal from the pixel can not be acquired accurately, the subject may be irradiated with excessive radiation, or the radiation dose may be insufficient to obtain an appropriate radiation image. There is a fear. In order to cope with this, the techniques described in Patent Documents 1 to 3 have been proposed as conventional techniques.

  Specifically, Patent Document 1 proposes a technique for performing correction so as to reduce the influence of crosstalk, using a signal from a correction wiring provided separately from the signal line connected to the pixel. Further, Patent Document 2 proposes a technique for correcting an output signal from a pixel and an output signal from a correction pixel having different sensitivities for detecting radiation to reduce the influence of crosstalk. ing. Moreover, in patent document 3, the influence by crosstalk is used using the sensor signal when the switch which outputs a sensor signal from the sensor for monitoring the irradiation amount of the incident radiation is turned on, and the sensor signal when turned off. There has been proposed a technique for correcting so as to reduce this.

Japanese Patent Laying-Open No. 2015-227851 JP, 2016-220116, A JP, 2016-25465, A

  For example, in order to improve the accuracy of detection of AEC such as detection of start of irradiation and detection of stop of irradiation described above, detection of integrated irradiation amount of radiation, etc., with respect to a detection signal for monitoring irradiation of radiation. Therefore, it is necessary to perform a suitable crosstalk component correction. However, in Patent Documents 1 to 3 described above, it is assumed that one correction method for correcting the crosstalk component is performed. For this reason, in Patent Documents 1 to 3, for example, it is suitable for a detection signal for monitoring the irradiation of radiation according to the time required for the correction processing of the crosstalk component, the degree of freedom of setting in the radiation detection region, and the like. There is a problem that it is difficult to correct the crosstalk component.

  The present invention has been made in view of such problems, and it is an object of the present invention to provide a mechanism capable of correcting a crosstalk component suitable for a detection signal for monitoring radiation irradiation.

The radiation imaging apparatus according to the present invention includes a first pixel for detecting at least one of detection of start of irradiation, detection of stop of irradiation, and detection of integrated irradiation amount of radiation. And a first output signal which is an output signal of the first pixel when the output switch of the first pixel is in a conducting state, and an output switch of the first pixel is not. A first correction method of correcting using a second output signal that is an output signal of the first pixel in the conductive state, and the other that the first output signal is different from the second output signal Switching means for switching and selecting a second correction method for correction using the output signal.
The present invention also includes a method for controlling the radiation imaging apparatus described above and a radiation imaging system having the radiation imaging apparatus described above.

  ADVANTAGE OF THE INVENTION According to this invention, it becomes possible to correct | amend a suitable crosstalk component with respect to the detection signal for monitoring radiation irradiation.

It is a figure which shows an example of schematic structure of the radiation imaging system which concerns on the 1st Embodiment of this invention. It is a figure which shows an example of schematic structure of the radiation imaging device which concerns on the 1st Embodiment of this invention. FIG. 3 is a view showing a first embodiment of the present invention, and showing an example of a schematic configuration of an imaging device control unit shown in FIG. 2; It is a figure which shows the 1st Embodiment of this invention and shows an example of the table memorize | stored in the memory shown in FIG. It is a flowchart which shows an example of the process sequence of the control method in the crosstalk component correction process by the radiation imaging device which concerns on the 1st Embodiment of this invention. It is a flowchart which shows an example of the process sequence of the control method in the crosstalk component correction process by the radiation imaging device which concerns on the 2nd Embodiment of this invention. It is a figure which shows the 2nd Embodiment of this invention, and shows an example of transition of the radiation dose irradiated to a radiation imaging device from the radiation source shown in FIG. FIG. 7 is a diagram showing a third embodiment of the present invention and showing an example of a schematic configuration of an imaging device control unit shown in FIG. 2; It is a flowchart which shows an example of the process sequence of the control method in the crosstalk component correction process by the radiation imaging device which concerns on the 3rd Embodiment of this invention. It is a figure which shows the 4th Embodiment of this invention, and shows an example of transition of the radiation dose irradiated from the radiation source (deterioration of a characteristic) shown in FIG. It is a flowchart which shows an example of the process sequence of the control method in the crosstalk component correction process by the radiation imaging device which concerns on the 4th Embodiment of this invention. It is a figure which shows an example of schematic structure of the radiation imaging system which concerns on the 5th Embodiment of this invention. It is a flowchart which shows an example of the process sequence of the control method in the crosstalk component correction process by the radiation imaging device which concerns on the 5th Embodiment of this invention. It is a figure which shows an example of schematic structure of the radiation imaging device which concerns on the 6th Embodiment of this invention.

  Hereinafter, embodiments (embodiments) for carrying out the present invention will be described with reference to the drawings.

First Embodiment
First, a first embodiment of the present invention will be described.

  FIG. 1 is a diagram showing an example of a schematic configuration of a radiation imaging system 10 according to a first embodiment of the present invention. As shown in FIG. 1, the radiation imaging system 10 is configured across a radiation room 100 for performing radiation imaging (radiation imaging) by radiation irradiation and a control room 200 installed in the vicinity of the radiation room 100.

  As one configuration of the radiation imaging system 10, in the radiation room 100, a radiation imaging apparatus 110, an access point 120, an AP communication cable 130, a communication control apparatus 140, a radiation generation apparatus communication cable 150, a radiation generation apparatus 160, and radiation imaging A device communication cable 170 is provided. Further, the radiation generation device 160 is configured to include a radiation generation control unit 161 and a radiation source 162.

  Further, as one configuration of the radiation imaging system 10, the control room 200 is provided with a control device 210, a radiation irradiation switch 220, an input device 230, a display device 240, and an in-hospital LAN 250.

  In addition, as one configuration of the radiation imaging system 10, a radiation room communication cable 300 that connects the communication control device 140 of the radiation room 100 and the control room 200 of the control room 200 so as to communicate with each other is provided.

  Hereinafter, each configuration of the radiation imaging system 10 illustrated in FIG. 1 will be described.

  The radiation imaging apparatus 110 is configured to include a power control unit 111 configured by a battery or the like, and a wireless communication unit 112. The radiation imaging apparatus 110 detects radiation emitted from the radiation source 162 and transmitted through the subject P1 as an image signal, and generates radiation image data.

  The access point 120 performs wireless communication with the radiation imaging apparatus 110. In radiation imaging system 10, access point 120 is used to relay communication between radiation imaging apparatus 110 and control apparatus 210.

  The AP communication cable 130 is a cable for communicably connecting the communication control device 140 and the access point 120.

  The communication control device 140 controls the radiation imaging device 110, the access point 120, the radiation generation device 160, and the control device 210 so that they can communicate with each other.

  The radiation generating apparatus communication cable 150 is a cable that communicably connects the communication control apparatus 140 and the radiation generating apparatus 160.

  The radiation generation controller 161 of the radiation generator 160 controls the radiation source 162 so as to irradiate radiation based on a predetermined irradiation condition. The radiation source 162 of the radiation generator 160 irradiates the subject P1 with radiation according to the control of the radiation generation control unit 161.

  The radiation imaging device communication cable 170 is a cable that communicably connects the communication control device 140 and the radiation imaging device 110.

  The control device 210 communicates with the radiation generation device 160 and the radiation imaging device 110 via the communication control device 140 to control the radiation imaging system 10 in an integrated manner.

  The radiation irradiation switch 220 inputs the timing of radiation irradiation by the operation of the operator P2.

  The input device 230 is a device for inputting input information related to an instruction from the operator P2, and for example, various input devices such as a keyboard and a touch panel are used.

  The display device 240 is a device that displays a radiation image subjected to image processing and a GUI, and for example, a display or the like is used.

  The in-hospital LAN 250 is an in-hospital backbone network.

  Next, an example of the operation of the radiation imaging system 10 shown in FIG. 1 will be described.

  First, when the operator P2 inputs the ID of the subject P1, the subject information such as the name and the date of birth, and the imaging information such as the imaging region of the subject P1 via the input device 230, the control device 210 sets the inputted subject information and imaging information of the subject P1. In the present embodiment, the subject information and the photographing information of the subject P1 are, for example, the examination order received via the in-hospital LAN 250 in addition to the mode in which the operator P2 directly inputs to the input device 230. It is also possible to apply a mode of automatically setting by selecting. In addition, it is also possible to apply an aspect in which the information of the imaging site is set by selecting a preset imaging protocol.

  Thereafter, the operator P2 fixes the posture of the subject P1 and the radiation imaging apparatus 110. This completes preparation for shooting.

  After the preparation for imaging is completed, when the operator P2 presses the radiation irradiation switch 220, the control device 210 detects this.

  Subsequently, the radiation generation device 160 performs a process of emitting radiation from the radiation source 162 toward the subject P1 based on the control of the control device 210 that has detected that the radiation irradiation switch 220 has been pressed. The radiation irradiated to the subject P1 passes through the subject P1 and enters the radiation imaging apparatus 110.

  The radiation imaging apparatus 110 wirelessly communicates with the radiation generation apparatus 160 to control the start and end of radiation irradiation. The radiation imaging apparatus 110 detects incident radiation as an image signal. At this time, the radiation imaging apparatus 110 is configured to include a plurality of conversion elements for converting the incident radiation into an image signal. For example, the conversion element may take a form including a scintillator that converts incident radiation into visible light and a photoelectric conversion element that converts visible light generated by the scintillator into an image signal that is an electrical signal. Further, for example, the conversion element may be a conversion element that directly converts incident radiation into an image signal that is an electrical signal. Furthermore, the radiation imaging apparatus 110 drives the conversion element to read the image signal, and the AD conversion unit converts the analog signal into a digital signal to generate radiation image data of the digital signal. The radiation image data generated by the radiation imaging apparatus 110 is transferred from the radiation imaging apparatus 110 to the control device 210 by wireless communication.

  The control device 210 performs image processing on the received radiation image data, and controls to display a radiation image based on the image processed radiation image data on the display device 240. The control device 210 that performs this process functions as an image processing device and a display control device.

  FIG. 2 is a view showing an example of a schematic configuration of a radiation imaging apparatus 110 according to the first embodiment of the present invention. The radiation imaging apparatus 110 includes, in addition to the power control unit 111 shown in FIG. 1, a radiation detection unit 113, an element power circuit unit 114, a driving circuit unit 115, a reading circuit unit 116, a signal processing unit 117, and imaging. An apparatus control unit 118 is included. Further, in the present embodiment, the wireless communication unit 112 shown in FIG. 1 is configured inside the imaging device control unit 118, as described later with reference to FIG.

  The power supply control unit 111 includes, for example, a battery, a DCDC converter, and the like. The power supply control unit 111 controls, for example, the element power supply circuit unit 114, and also performs drive control of the analog circuit power supply and drive control of the digital circuit power supply that performs wireless communication and the like.

  The radiation detection unit 113 includes a plurality of pixels that detect incident radiation. Specifically, as shown in FIG. 2, the radiation detection unit 113 is configured to have a plurality of pixels arranged to form a plurality of rows and a plurality of columns. Here, an area where a plurality of pixels are arranged in the radiation detection unit 113 is defined as an imaging area.

  The radiation detection unit 113 includes detection pixels 1131 and correction pixels 1132 as a plurality of pixels. The detection pixel 1131 detects at least the timing at which the irradiation of the radiation from the radiation source 162 is started, the detection of the timing at which the irradiation of the radiation should be stopped, and the detection of the irradiation amount of the radiation or the integrated irradiation amount. It is a first pixel for performing any one detection. Further, the correction pixel 1132 is a second pixel for reducing the above-described crosstalk component, and the detection pixel 1131 is a pixel (for example, a pixel with low sensitivity) having a different sensitivity for detecting radiation.

  The detection pixel 1131 includes a first conversion element 11311 that converts radiation into an image signal that is an electrical signal, and a first switch 11312 that is an output switch disposed between the first conversion element 11311 and the column signal line 1135. Is configured. The first conversion element 11311 includes, for example, a scintillator that converts incident radiation into visible light, and a photoelectric conversion element that converts visible light generated by the scintillator into an image signal that is an electrical signal. In this case, the scintillator is, for example, formed in a sheet shape so as to cover the imaging region, and can take a form shared by a plurality of pixels. The first conversion element 11311 may be, for example, a conversion element that directly converts incident radiation into an image signal. The first switch 11312 includes, for example, a thin film transistor (TFT) formed of a semiconductor such as amorphous silicon or polycrystalline silicon (preferably polycrystalline silicon) to form an active region.

  The correction pixel 1132 basically has the same configuration as the detection pixel 1131, and includes a second conversion element 11321 and a second switch 11322 which is an output switch. As described above, the correction pixel 1132 is different from the detection pixel 1131 in the sensitivity for detecting the incident radiation. For example, the correction pixel 1132 has a smaller area for detecting radiation than the detection pixel 1131 in order to output an electric signal different from the detection pixel 1131 to the incident radiation, and the sensitivity for detecting the radiation is small. It may take the form of low pixels. When the correction pixel 1132 takes the form of a pixel whose sensitivity for detecting radiation is lower than that of the detection pixel 1131, the pixel for detecting the above-mentioned crosstalk component has a sensitivity of substantially zero. Is more preferable.

  For example, in the case of the radiation detection unit 113 that directly converts radiation into an electric signal, a shielding member using heavy metal such as lead is provided on the second conversion element 11321 of the correction pixel 1132 as a shielding member that shields radiation. Further, it is possible to adopt a form in which the radiation detection area is reduced. Further, for example, in the case of the indirect type radiation detection unit 113 that converts radiation into light using a scintillator and converts this light into an electric signal, for example, an aluminum shielding film or the like is used as the shielding member in the first correction pixel 1132. You may provide between 2 conversion element 11321 and a scintillator. In any of the conversion-type radiation detection units 113, the shielding member that blocks radiation is disposed in a region that overlaps at least a part of the second conversion element 11321 of the correction pixel 1132 in a plan view with respect to the imaging region. Good.

  In the imaging region, only one area of the detection pixel 1131 and the area of the correction pixel 1132 may be disposed, or a plurality of areas may be disposed.

  Further, in the radiation detection unit 113, a plurality of bias lines 1133, a plurality of drive lines 1134, and a plurality of column signal lines 1135 are provided. The bias line 1133 is a wiring for supplying the bias voltage Vs to each pixel from the element power supply circuit unit 114. In the example shown in FIG. 2, one bias line 1133 is connected in the column direction of each pixel. . The drive line 1134 is a wiring for supplying a drive signal from the drive circuit unit 115 to each pixel. In the example shown in FIG. 2, one drive line 1134 is connected in the row direction of each pixel. The column signal line 1135 is a wiring for outputting an output signal from each pixel to the readout circuit unit 116. In the example shown in FIG. 2, one column signal line 1135 is connected in the column direction of each pixel. Yes.

  The first electrode of the first conversion element 11311 is connected to the first main electrode of the first switch 11312, and the second electrode of the first conversion element 11311 is connected to the bias line 1133. Similarly, the first electrode of the second conversion element 11321 is connected to the first main electrode of the second switch 11322, and the second electrode of the second conversion element 11321 is connected to the bias line 1133. Here, one bias line 1133 is commonly connected to the second electrodes of the plurality of conversion elements arranged in the column direction.

  The second main electrode of the first switch 11312 and the second main electrode of the second switch 11322 are connected to the column signal line 1135. The control electrode of the first switch 11312 and the control electrode of the second switch 11322 are connected to the drive line 1134.

  The element power supply circuit unit 114 supplies a bias voltage Vs to each pixel through the plurality of bias lines 1133 based on the control of the power supply control unit 111.

  The drive circuit unit 115 supplies a drive signal to each pixel through each drive line in the plurality of drive lines 1134 based on the control of the imaging device control unit 118.

  The read out circuit unit 116 is a circuit unit that reads out an output signal from each pixel through the plurality of column signal lines 1135 based on the control of the imaging device control unit 118. The read circuit unit 116 includes a plurality of detection units 1161, a multiplexer 1162, and an analog-to-digital converter (hereinafter, referred to as “AD conversion unit”) 1163.

  The plurality of detection units 1161 are provided corresponding to the plurality of column signal lines 1135. That is, one column signal line 1135 is connected to one detection unit 1161. The detection unit 1161 includes, for example, a differential amplifier, and reads and detects an output signal of a pixel connected to the column signal line 1135 via the corresponding column signal line 1135.

  The multiplexer 1162 selects the plurality of detection units 1161 in a predetermined order, and outputs the signal from the selected detection unit 1161 to the AD conversion unit 1163.

  The AD conversion unit 1163 converts the signal from the detection unit 1161 supplied via the multiplexer 1162 into a digital signal, and outputs the digital signal to the signal processing unit 117.

  The signal processing unit 117 processes a signal output from the readout circuit unit 116 (specifically, the AD conversion unit 1163) based on the control of the imaging device control unit 118. Specifically, the signal processing unit 117 performs, for example, processing of detection of irradiation of radiation, calculation of the irradiation amount of radiation, and calculation of integrated irradiation amount as information indicating irradiation of radiation to the radiation imaging apparatus 110. In the signal output from the read out circuit unit 116, the potential fluctuation of the electrode of the detection pixel 1131 caused by the radiation irradiation is caused through the parasitic capacitance existing between the electrode of the detection pixel 1131 and the column signal line 1135. The resulting crosstalk component is included. Therefore, the radiation imaging apparatus 110 (for example, the imaging apparatus control unit 118) according to the present embodiment performs correction processing for removing the crosstalk component in order to accurately detect the irradiation amount of the incident radiation.

  In the present embodiment, for example, the imaging device control unit 118, when the first switch 11312 (output switch) of the detection pixel 1131 (first pixel) is in a conductive state, as a correction method for removing the crosstalk component described above. The first output signal which is the output signal of the detection pixel 1131 is corrected using the second output signal which is the output signal of the first pixel 1131 when the above-described first switch 11312 is nonconductive. Two methods may be implemented: a first correction method, and a second correction method of correcting the first output signal described above using another output signal different from the second output signal described above. Here, in the present embodiment, the first output signal corresponds to a detection signal for monitoring the irradiation of the radiation from the radiation source 162.

  Specifically, in this embodiment, when the first correction method is performed, the first switch 11312 is turned on while radiation is incident on the radiation detection unit 113, and the detection pixel 1131 is detected in the readout circuit unit 116. The second output signal read out from the detection pixel 1131 in the read out circuit unit 116 with the first switch 11312 turned off while the radiation is incident on the radiation detection unit 113. Correction is performed using the signal to correct the crosstalk component. In the case of this first correction method, it is possible to adopt an aspect of correcting the crosstalk component by subtracting the above-mentioned second output signal from the above-mentioned first output signal in more detail.

  In the present embodiment, when the second correction method is performed, the first switch 11312 of the detection pixel 1131 is turned on while radiation is incident on the radiation detection unit 113, and at the same time, the correction pixel 1132 is turned on. The second switch 11322 is turned on, and the first output signal of the detection pixel 1131 read out by the readout circuit unit 116 is corrected using the output signal of the correction pixel 1132 which is another output signal. , Correct the crosstalk component. In the case of the second correction method, more specifically, a method of correcting the crosstalk component is adopted by subtracting the output signal of the correction pixel 1132 from the first output signal described above.

  The second correction method described above can be implemented only with the read-out time when the first switch 11312 is in the conductive state, and therefore, the time related to the correction processing of the crosstalk component (for example, This is a correction method suitable when the radiation exposure time is short. Further, since the first correction method described above has no spatial correction error because it uses the same output signal of the detection pixel 1131, it is possible to use a crosstalk component with higher accuracy compared to the second correction method. This correction method is suitable when correction is required. According to the first correction method, for example, even when a pixel whose output is largely different in the radiation detection area (ROI) is included, it is possible to reduce the correction error.

  In addition to the process of setting and switching the first correction method and the second correction method described above, the imaging device control unit 118 performs processing based on the information output from the signal processing unit 117 and the control command from the control device 210. The driving circuit unit 115, the reading circuit unit 116, and the like are controlled. The imaging device control unit 118 can be connected to a radiation imaging device communication cable 170 for communicating with the communication control device 140.

  FIG. 3 is a diagram illustrating an example of a schematic configuration of the imaging device control unit 118 illustrated in FIG. 2 according to the first embodiment of this invention. As shown in FIG. 3, the imaging device control unit 118 includes a drive control unit 1181, a CPU 1182, a memory 1183, a radiation generation device control unit 1184, an image data control unit 1185, a communication switching unit 1186, a wireless communication unit 112, and a wired connection. The communication unit 1187 is included.

  The drive control unit 1181 controls the element power supply circuit unit 114, the drive circuit unit 115, and the read circuit unit 116 as necessary based on the information output from the signal processing unit 117 and the control command from the control device 210. , Signal processing unit 117 and the like. At this time, information on the imaging region is also included in the control command, and the drive control unit 1181 refers to a table of the imaging region and radiation irradiation conditions recorded in the memory 1183. As a result, the drive control unit 1181 selects one correction method from the first correction method and the second correction method described above, and based on the selected correction method, the drive circuit unit 115, the read circuit unit 116, and the signal The processing unit 117 and the like are controlled to perform crosstalk component correction processing.

  The CPU 1182 controls the radiation imaging apparatus 110 as a whole using programs and various data stored in the memory 1183.

  The memory 1183 stores, for example, programs and various data used when the CPU 1182 executes processing. These various types of data include a table indicating the correspondence between the imaging region and the radiation irradiation condition, which is referred to when the crosstalk component correction method executed by the drive control unit 1181 is selected. Also, the memory 1183 stores various data obtained by the processing of the CPU 1182 and various radiation image data.

  FIG. 4 is a diagram showing the first embodiment of the present invention and showing an example of a table stored in the memory 1183 shown in FIG. FIG. 4 shows the correspondence between the imaging site and the radiation irradiation conditions (tube voltage and tube current of the radiation source 162, irradiation time (for example, maximum irradiation time), mAs value, SID) corresponding to the imaging site. A table is shown. In the present embodiment, in addition to the radiation irradiation conditions shown in FIG. 4, the appropriate dose of radiation is also stored in the memory 1183 in association with the imaging site as the radiation irradiation conditions.

  The radiation generating apparatus control unit 1184 controls the radiation generating apparatus 160 based on the information output from the signal processing unit 117 and the information from the drive control unit 1181. For example, the radiation generation apparatus control unit 1184 and the radiation generation apparatus 160 (specifically, the radiation generation control unit 161) are information related to control of the radiation generation apparatus 160 (for example, notification of radiation start and stop of radiation, radiation Exchange of the irradiation amount and the integrated irradiation amount).

  The image data control unit 1185 controls to store radiation image data based on information output from the signal processing unit 117 in the memory 1183 and controls communication with the control device 210. The image data control unit 1185 and the control device 210 exchange radiation image data and control-related information (for example, control commands).

  The communication switching unit 1186 enables the communication of the wired communication unit 1187 when the radiation imaging apparatus communication cable 170 is connected to the radiation imaging apparatus 110, and wireless communication when the radiation imaging apparatus communication cable 170 is disconnected. Switching to enable communication of the unit 112 is performed.

  The wireless communication unit 112 communicates with the communication control device 140 via the access point 120.

  The wired communication unit 1187 communicates with the communication control device 140 via the radiation imaging device communication cable 170.

  Next, a processing procedure of a control method of the radiation imaging system 10 including the radiation imaging apparatus 110 will be described.

  A radiation detection area (ROI) which is an area where the operator P2 is to monitor radiation conditions (which may include the appropriate dose of radiation in addition to the irradiation conditions shown in FIG. 4) or the radiation via the input device 230; When the information on the imaging region or the like is input, the control device 210 detects this. Then, the control device 210 transmits the inputted radiation irradiation condition, radiation detection area (ROI), information of the imaging region, etc. to the radiation imaging device 110 and the radiation generation device 160 via the communication control device 140.

  When the imaging preparation is completed and the operator P2 presses the radiation irradiation switch 220, the control device 210 detects this. Then, the control device 210 performs control of irradiating radiation from the radiation generation device 160 toward the subject P1. The radiation emitted from the radiation generator 160 passes through the subject P 1 and enters the radiation imaging device 110.

  The radiation imaging apparatus 110 detects the radiation incident on the radiation detection region (ROI) by the detection pixel 1131, and calculates an integrated dose that is an integrated value of the dose (arrival dose) detected in a predetermined period by the signal processing unit 117. Calculate. Then, the imaging apparatus control unit 118 calculates an appropriate dose from the integrated irradiation amount information from the signal processing unit 117 and the information on the imaging region and the radiation irradiation condition input by the operator P2, and determines the radiation irradiation stop timing.

  The radiation imaging apparatus 110 notifies the radiation generation apparatus 160 of the stop by, for example, wireless communication based on the radiation irradiation stop timing determined by the imaging apparatus control unit 118. Thereafter, the radiation generation device 160 stops the radiation application based on the notified radiation application stop timing. Here, the radiation imaging apparatus 110 notifies the stop of radiation irradiation as a detection result of detecting radiation, but the present embodiment is not limited to this aspect. For example, a mode in which the radiation imaging apparatus 110 transmits, to the radiation generation apparatus 160, an arrival dose for each predetermined time as a detection result, and the radiation generation apparatus 160 calculates the integrated value of the arrival dose is also applicable to this embodiment. is there.

  Next, a processing procedure of a control method in the crosstalk component correction process by the radiation imaging apparatus 110 will be described.

  FIG. 5 is a flowchart showing an example of a processing procedure of a control method in crosstalk component correction processing by the radiation imaging apparatus 110 according to the first embodiment of the present invention.

  First, in step S <b> 501, the imaging device control unit 118 determines whether imaging information such as an imaging region has been received from the control device 210. If the result of this determination is that imaging information such as the imaging region has not yet been received from the control device 210 (S501 / N), the process waits in step S501 until imaging information such as the imaging region is received from the control device 210. .

  On the other hand, as a result of the determination in step S501, when imaging information such as an imaging region is received from the control device 210 (S501 / Y), the process proceeds to step S502. In step S502, the imaging device control unit 118 acquires the irradiation time and the appropriate dose from the table stored in the memory 1183 based on the received information on the imaging region.

  Subsequently, in step S503, the imaging apparatus control unit 118 determines whether the irradiation time acquired in step S502 is less than a predetermined threshold. The predetermined threshold value in step S503 is set as a predetermined threshold value t. In addition, it is preferable that the predetermined threshold t be, for example, the shortest irradiation time that can be dealt with by the crosstalk component correction method (first correction method) that does not use the output signal of the correction pixel 1132.

  If it is determined in step S503 that the irradiation time obtained in step S502 is less than the predetermined threshold (irradiation time <predetermined threshold t) (S503 / Y), the process proceeds to step S504. In step S504, the imaging apparatus control unit 118 selects a second correction method for correcting the crosstalk component using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component. Then, the imaging device control unit 118 notifies the drive circuit unit 115, the readout circuit unit 116, the signal processing unit 117, and the like that the second correction method has been selected.

  Subsequently, in step S505, the imaging device control unit 118 causes the first switch 11312 of the detection pixel 1131 to be in a conduction state while radiation is incident on the radiation detection unit 113 with respect to the drive circuit unit 115. At the same time, drive control is performed to turn on the second switch 11322 of the correction pixel 1132. At the same time, the imaging device control unit 118 reads the first output signal, which is the output signal of the detection pixel 1131, to the read out circuit unit 116 when the first switch 11312 is in the on state, and the second switch 11322 Control is performed so that the output signal of the correction pixel 1132 is read when is in the conductive state. After that, the imaging device control unit 118 (or the signal processing unit 117) subtracts the output signal of the correction pixel 1132 from the first output signal of the detection pixel 1131 read by the reading circuit unit 116, A process for correcting the crosstalk component is performed.

  Subsequently, in step S506, the imaging device control unit 118 determines whether the integrated irradiation amount output from the signal processing unit 117 is larger than the appropriate dose acquired in step S502. As a result of this determination, if the integrated irradiation dose is not larger than the appropriate dose (that is, the integrated irradiation dose is less than the appropriate dose) (S506 / N), the process returns to the process of step S505. On the other hand, as a result of the determination in step S506, when the integrated irradiation amount is larger than the appropriate dose (S506 / Y), the process proceeds to step S510.

  If the result of determination in step S503 is that the irradiation time acquired in step S502 is not less than the predetermined threshold (irradiation time is equal to or greater than the predetermined threshold (irradiation time ≧ predetermined threshold t)) (S503 / N) Go to step S507. In step S507, the imaging device control unit 118 uses the second output signal of the detection pixel 1131 described above without using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component. A first correction method for correcting the crosstalk component is selected. Then, the imaging apparatus control unit 118 notifies the driving circuit unit 115, the reading circuit unit 116, the signal processing unit 117, and the like that the first correction method has been selected.

  Subsequently, in step S508, the imaging device control unit 118 turns on the first switch 11312 while radiation is incident on the radiation detection unit 113 with respect to the drive circuit unit 115 and the readout circuit unit 116. The control for reading out the first output signal from the detection pixel 1131 and the control for reading out the second output signal from the detection pixel 1131 by turning off the first switch 11312 are alternately performed. Thereafter, the imaging apparatus control unit 118 (or the signal processing unit 117) subtracts the second output signal of the detection pixel 1131 from the first output signal of the detection pixel 1131 read by the read circuit unit 116. Thus, processing for correcting the crosstalk component is performed.

  Subsequently, in step S509, the imaging device control unit 118 determines whether the integrated irradiation amount output from the signal processing unit 117 is larger than the appropriate dose acquired in step S502. As a result of this determination, if the integrated irradiation dose is not larger than the appropriate dose (that is, the integrated irradiation dose is less than the appropriate dose) (S509 / N), the process returns to the process of step S508. On the other hand, as a result of the determination in step S509, when the integrated irradiation amount is larger than the appropriate dose (S509 / Y), the process proceeds to step S510.

  In step S510, the imaging device control unit 118 notifies the radiation generation device 160 of the stop of radiation irradiation, for example, by wireless communication.

  When the process of step S510 ends, the process of the flowchart shown in FIG. 5 ends.

  In the process of the flowchart shown in FIG. 5 described above, the imaging device control unit 118 uses the output signal of the correction pixel 1132 depending on whether the irradiation time of the radiation is less than the predetermined threshold (S 503). A second correction method (S504, S505) for correcting the crosstalk component, and a second correction method for correcting the crosstalk component using the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132. A process of switching and selecting one of the correction methods (S507 and S508) is performed. The imaging device control unit 118 that performs this process constitutes a switching unit. According to such a configuration, the second correction method can be selected in the case of imaging with a short irradiation time of radiation that does not allow a long time for correction processing of the crosstalk component. Then, the first correction method can be selected in the case of imaging with a long irradiation time of radiation that is permitted to be long for the crosstalk component correction process. This makes it possible to correct the crosstalk component appropriately, and as a result, it is also possible to improve the accuracy of the AEC.

<Modification of First Embodiment>
Below, the modification of 1st Embodiment is demonstrated.

  Although the first embodiment of the present invention described above has a mode in which a suitable crosstalk component correction method is determined using imaging information such as a received imaging region or the like, the present invention is limited to this mode. is not. For example, information on a crosstalk component correction method to be executed by the operator P2 in addition to the imaging information described above is input to the input device 230, and the imaging device control unit 118 that has received the information on the crosstalk component correction method performs the crosstalk A mode in which a component correction method is selected and executed can also be applied. In the case of taking this form, for example, when the crosstalk component correction method selected according to the input information input to the input device 230 is not appropriate for the setting of the imaging conditions, the imaging device control unit 118 notifies that effect. Control to notify the operator P2 is performed. Specifically, for example, the imaging device control unit 118 performs control to display a warning on the display device 240 that the crosstalk component correction method designated by the operator P2 is not appropriate, and notifies the operator P2. The imaging device control unit 118 that performs the notification constitutes a notification unit.

  Further, in the first embodiment of the present invention described above, irradiation of radiation from the radiation source 162 is started as the first pixel having a sensitivity for detecting radiation different from that of the correction pixel 1132 which is the second pixel. The detection pixel 1131 is used to detect at least one of detection of the timing, detection of the timing at which the irradiation of the radiation should be stopped, and detection of the irradiation amount of the radiation and the integrated irradiation amount. It was. However, the present invention is not limited to this form. For example, a mode in which the detection pixel 1131 used as the first pixel also has a function as an imaging pixel for acquiring a radiation image is also applicable to the present invention. Moreover, the form which provides the pixel 1131 for a detection mentioned above separately from the pixel for an imaging mentioned above as another form is also applicable to this invention.

Second Embodiment
Next, a second embodiment of the present invention will be described. In the description of the second embodiment described below, the description of matters in common with the first embodiment described above is omitted, and matters different from the first embodiment described above will be described. Further, in the description of the second embodiment described below, configurations and processing steps common to those of the above-described first embodiment are given the same reference numerals for description.

  The schematic configuration of the radiation imaging system according to the second embodiment is the same as the schematic configuration of the radiation imaging system 10 according to the first embodiment shown in FIG. The schematic configuration of the radiation imaging apparatus according to the second embodiment is the same as the schematic configuration of the radiation imaging apparatus 110 according to the first embodiment shown in FIG. The schematic configuration of the imaging device control unit according to the second embodiment is the same as the schematic configuration of the imaging device control unit 118 according to the first embodiment shown in FIG.

  However, in the second embodiment, the signal processing unit 117 illustrated in FIG. 2 outputs the radiation dose irradiated at predetermined time intervals together with the cumulative radiation dose. Here, the predetermined time is, for example, a readout cycle of the output signal of each pixel in the radiation detection area (ROI). In addition, the drive control unit 1181 compares the radiation dose irradiated for each predetermined time output from the signal processing unit 117 with a predetermined threshold, and switches and selects the crosstalk component correction method according to the result. Shall. Further, in the second embodiment, at the start of radiation irradiation, the second correction method using the output signal of the correction pixel 1132 capable of coping with a short irradiation time is selected, and drive control therefor is performed. Shall.

  FIG. 6 is a flowchart showing an example of a processing procedure of a control method in crosstalk component correction processing by the radiation imaging apparatus 110 according to the second embodiment of the present invention.

  First, in step S601, the imaging device control unit 118 selects a second correction method for correcting the crosstalk component using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component as an initial setting. To do. Then, the imaging device control unit 118 notifies the drive circuit unit 115, the readout circuit unit 116, the signal processing unit 117, and the like that the second correction method has been selected.

  Subsequently, in step S <b> 602, the imaging device control unit 118 determines whether or not the radiation dose irradiated at predetermined time intervals output from the signal processing unit 117 has been output more than 0 twice or more. Here, the reason why the radiation dose emitted every predetermined time is greater than 0 twice or more is because the drive start timing of the drive circuit unit 115 by the drive control unit 1181 is the radiation start timing of the radiation from the radiation source 162 Is not necessarily simultaneous. This will be described with reference to FIG.

  FIG. 7 shows the second embodiment of the present invention and is a diagram showing an example of the transition of the radiation dose irradiated to the radiation imaging apparatus 110 from the radiation source 162 shown in FIG. In FIG. 7, the horizontal axis represents time, and the vertical axis represents the radiation dose (radiation dose) applied to the radiation imaging apparatus 110. And in FIG. 7, the drive start timing of the circuit part 115 for a drive is made into time T0, and the example which calculates a radiation dose at the time of time T1, T2, T3, T4 by a fixed space | interval is shown. In the example shown in FIG. 7, the time T0 which is the drive start timing of the drive circuit unit 115 is different from the time X0 which is the irradiation start timing of the radiation from the radiation source 162 (the drive start timing is earlier) ). Then, as shown in FIG. 7, when the drive start timing is earlier, the first output from the signal processing unit 117 after the radiation start is the radiation dose between time T0 and time T1, The value is smaller than the irradiation amount for a predetermined time. For this reason, in the present embodiment, in step S602, it is determined whether or not the radiation dose irradiated at each predetermined time output from the signal processing unit 117 has an output that is greater than 0 twice or more. In the case of the example shown in FIG. 7, when the radiation dose between time T1 and time T2 is output from the signal processing unit 117 (from the predetermined time thereafter (from time T2 to time T3, from time T3 to time T4 Similarly, in the case of an interval), it is determined that there is an output greater than 0 twice or more.

  Then, as a result of the determination in step S602, when the radiation dose irradiated every predetermined time has not yet been output more than twice (S602 / N), the radiation dose irradiated every predetermined time is The process waits in step S602 until there is an output greater than 0 twice or more.

  On the other hand, as a result of the determination in step S602, if there is an output in which the radiation dose emitted for each predetermined time is greater than 0 twice or more (S602 / Y), the process proceeds to step S603. In step S603, the imaging apparatus control unit 118 determines whether the radiation dose emitted at predetermined time intervals is less than a predetermined threshold value. The predetermined threshold value in step S603 is set as a predetermined threshold value A.

  Here, the predetermined threshold A can be calculated as follows, for example. For example, from a radiation exposure time and an appropriate dose that can be handled by the crosstalk component correction method (first correction method) that does not use the output signal of the correction pixel 1132, per predetermined time that can be handled by the first correction method. The upper limit value of the irradiation dose can be applied as the predetermined threshold A. Further, for example, it is possible to calculate and apply the predetermined threshold A from the information of the irradiation dose per predetermined time, the reading cycle in the output signal of each pixel of the radiation detection area (ROI), and the appropriate dose.

  As a result of the determination in step S603, the radiation dose irradiated every predetermined time is not less than the predetermined threshold (the radiation dose per predetermined time is equal to or greater than the predetermined threshold (the radiation dose per predetermined time ≧ the predetermined threshold). If (A)) (S603 / N), the process waits in step S603. In this case, the imaging device control unit 118 maintains the selection of the second correction method for correcting the crosstalk component using the output signal of the correction pixel 1132 set in step S601. Then, the imaging device control unit 118 notifies the driving circuit unit 115, the reading circuit unit 116, the signal processing unit 117, and the like that the selection of the second correction method is maintained. Thereafter, the imaging apparatus control unit 118 (or the signal processing unit 117) performs drive control, crosstalk component correction processing, and the like based on the second correction method.

  On the other hand, as a result of the determination in step S603, if the radiation dose emitted every predetermined time is less than the predetermined threshold (the radiation dose every predetermined time <predetermined threshold A) (S603 / Y), the step The process proceeds to S507. In step S507, the imaging device control unit 118 uses the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component. A first correction method for correcting the component is selected. Then, the imaging apparatus control unit 118 notifies the driving circuit unit 115, the reading circuit unit 116, the signal processing unit 117, and the like that the first correction method has been selected. Thereafter, the processes of steps S508, S509, and S510 shown in FIG. 5 are performed.

  Then, when the process of step S510 ends, the process of the flowchart shown in FIG. 6 ends.

  In the processing of the flowchart shown in FIG. 6 described above, the imaging device control unit 118 determines whether the correction pixel 1132 includes the correction pixel 1132 according to whether or not the radiation dose irradiated every predetermined time is less than a predetermined threshold (S603). The second correction method (S601) for correcting the crosstalk component using the output signal, and the crosstalk component using the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132 The first correction method (S507, S508) for correcting the image is switched and selected. The imaging device control unit 118 that performs this process constitutes a switching unit. According to this configuration, the second correction method is used in the case of imaging with a short radiation irradiation time (for example, time T2 or time T3 shown in FIG. 7) in which the time for correction processing of the crosstalk component is not long. You can choose. Then, the first correction method is selected in the case of radiography (for example, time T4 shown in FIG. 7 or a later time shown in FIG. 7) in which the radiation irradiation time for which the time relating to the correction process of the crosstalk component is allowed is long can do. Thereby, it is possible to correct a suitable crosstalk component, and as a result, it is possible to improve the accuracy of AEC.

Third Embodiment
Next, a third embodiment of the present invention will be described. In the description of the third embodiment described below, the description of matters common to the first and second embodiments described above will be omitted, and the matters different from the first and second embodiments described above I will explain. Further, in the description of the third embodiment described below, configurations and processing steps common to those in the first and second embodiments described above are given the same reference numerals for description.

  The schematic configuration of the radiation imaging system according to the third embodiment is the same as the schematic configuration of the radiation imaging system 10 according to the first embodiment shown in FIG. The schematic configuration of the radiation imaging apparatus according to the third embodiment is the same as the schematic configuration of the radiation imaging apparatus 110 according to the first embodiment shown in FIG.

  FIG. 8 is a diagram illustrating an example of a schematic configuration of the imaging device control unit 118 illustrated in FIG. 2 according to the third embodiment of the present invention. As shown in FIG. 8, the imaging device control unit 118 according to the third embodiment is configured to further include a timer 1188 in addition to the configuration shown in FIG.

  The timer 1188 measures, for example, the time from the start of drive control by the drive control unit 1181 by the imaging device control unit 118.

  FIG. 9 is a flowchart showing an example of a processing procedure of a control method in crosstalk component correction processing by the radiation imaging apparatus 110 according to the third embodiment of the present invention.

  First, in step S601, as in the second embodiment, the imaging device control unit 118 uses the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component as an initial setting. The second correction method to be corrected is selected. Then, the imaging device control unit 118 notifies the drive circuit unit 115, the readout circuit unit 116, the signal processing unit 117, and the like that the second correction method has been selected.

  Subsequently, in step S <b> 901, the imaging device control unit 118 starts time measurement from the drive control start time in the timer 1188 at the same time that the drive control unit 1181 starts drive control.

  Subsequently, in step S902, the imaging device control unit 118 determines whether or not a predetermined time has elapsed since the drive control unit 1181 started the drive control based on the current time measurement of the timer 1188. Here, the predetermined time is a time that can be dealt with by the crosstalk component correction method (first correction method) that does not use the output signal of the correction pixel 1132, for example, for each pixel in the radiation detection region (ROI). It is possible to calculate from the read cycle in the output signal.

  If it is determined in step S902 that the predetermined time has not elapsed since the drive control unit 1181 started the drive control (S902 / N), the process waits in step S902. In this case, the imaging apparatus control unit 118 maintains the selection of the second correction method for correcting the crosstalk component using the output signal of the correction pixel 1132 set in step S601. Then, the imaging device control unit 118 notifies the driving circuit unit 115, the reading circuit unit 116, the signal processing unit 117, and the like that the selection of the second correction method is maintained. Thereafter, the imaging apparatus control unit 118 (or the signal processing unit 117) performs drive control, crosstalk component correction processing, and the like based on the second correction method.

  On the other hand, as a result of the determination in step S902, when a predetermined time has elapsed since the drive control unit 1181 started the drive control (S902 / Y), the process proceeds to step S507. In step S507, the imaging device control unit 118 uses the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component. A first correction method for correcting the component is selected. Then, the imaging apparatus control unit 118 notifies the driving circuit unit 115, the reading circuit unit 116, the signal processing unit 117, and the like that the first correction method has been selected. Thereafter, the processes of steps S508, S509, and S510 shown in FIG. 5 are performed.

  Then, when the process of step S510 ends, the process of the flowchart shown in FIG. 9 ends.

  In the process of the flowchart shown in FIG. 9 described above, the imaging device control unit 118 uses the output signal of the correction pixel 1132 depending on whether or not a predetermined time has elapsed since the start of drive control (S902). Then, the second correction method (S601) for correcting the crosstalk component and the second correction signal for correcting the crosstalk component using the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132 are used. A process of switching and selecting one of the correction methods (S507 and S508) is performed. The imaging device control unit 118 that performs this process constitutes a switching unit. According to such a configuration, the second correction method can be selected in the case of imaging with a short irradiation time of radiation that does not allow a long time for correction processing of the crosstalk component. Then, the first correction method can be selected in the case of imaging with a long irradiation time of radiation that is permitted to be long for the crosstalk component correction process. Thereby, it is possible to correct a suitable crosstalk component, and as a result, it is possible to improve the accuracy of AEC.

<Modification of Third Embodiment>
In the third embodiment of the present invention described above, the crosstalk component correction method is switched when a predetermined time has elapsed since the drive control unit 1181 started the drive control. It is not limited to the form. For example, a mode in which the crosstalk component correction method is switched when a predetermined time has elapsed after the drive control unit 1181 receives a drive control command is also applicable to the present invention.

Fourth Embodiment
Next, a fourth embodiment of the present invention will be described. In the description of the fourth embodiment described below, the description of matters in common with the first to third embodiments described above is omitted, and the matters different from the first to third embodiments described above I will explain. Further, in the description of the fourth embodiment described below, configurations and processing steps common to those in the first to third embodiments described above are given the same reference numerals for description.

  The schematic configuration of the radiation imaging system according to the fourth embodiment is the same as the schematic configuration of the radiation imaging system 10 according to the first embodiment shown in FIG. The schematic configuration of the radiation imaging apparatus according to the fourth embodiment is the same as the schematic configuration of the radiation imaging apparatus 110 according to the first embodiment shown in FIG. The schematic configuration of the imaging device control unit according to the fourth embodiment is the same as the schematic configuration of the imaging device control unit 118 according to the third embodiment shown in FIG.

  In the first to third embodiments described above, the crosstalk component correction method is switched according to the irradiation time of the radiation, the radiation amount irradiated for each predetermined time, and the time from the start of the drive control. It was. However, in radiation imaging (radiography) using a radiation source 162 whose characteristics have deteriorated due to aging, radiation emitted from the radiation source 162 may not be stable.

  FIG. 10 is a diagram showing an example of the transition of the radiation dose irradiated from the radiation source 162 shown in FIG. 1 (deteriorated characteristics) according to the fourth embodiment of the present invention. In FIG. 10, time is taken on the horizontal axis and the radiation dose (radiation dose) emitted from the radiation source 162 is taken on the vertical axis. And, in FIG. 10, similarly to FIG. 7, an example in which the drive start timing of the drive circuit unit 115 is time T0, and the radiation dose is calculated at time T1, T2, T3, T4 at regular intervals . As shown in FIG. 10, the radiation dose may not be stable in the radiation source 162 whose characteristics have deteriorated. In this case, it may occur that the crosstalk component correction method selected based on, for example, the setting of the imaging region is not appropriate. Therefore, in the fourth embodiment, the second correction method of correcting the crosstalk component using the output signal of the correction pixel 1132 is the crosstalk component simultaneously with the detection of the radiation exposure dose using the correction pixel 1132 An example of switching to a suitable crosstalk component correction method will be described by paying attention to the fact that there is no temporal correction error because the signal is acquired.

  In the fourth embodiment, the signal processing unit 117 illustrated in FIG. 2 outputs the radiation dose irradiated every predetermined time together with the cumulative radiation dose. Here, the predetermined time is, for example, a readout cycle of the output signal of each pixel in the radiation detection area (ROI). In addition, the drive control unit 1181 calculates the difference between the radiation dose emitted at predetermined time intervals output from the signal processing unit 117 and the previously obtained radiation dose, and compares the difference value with a predetermined threshold value. According to the result, the crosstalk component correction method is switched and selected.

  FIG. 11 is a flowchart illustrating an example of a processing procedure of a control method in the crosstalk component correction processing by the radiation imaging apparatus 110 according to the fourth embodiment of the present invention.

  First, in step S1101, the imaging device control unit 118 sets a crosstalk component correction method according to the imaging region, similarly to the processing of the flowchart shown in FIG. 5 in the first embodiment.

  Subsequently, in step S602, as in the second embodiment, the imaging device control unit 118 outputs a radiation amount greater than 0 twice or more for each predetermined time output from the signal processing unit 117. Determine if there was. As a result of this determination, when the radiation dose irradiated every predetermined time does not yet have an output larger than 0 twice or more (S602 / N), the radiation dose irradiated every predetermined time is twice or more 0 In step S602, the process waits until there is a larger output.

  On the other hand, as a result of the determination in step S602, if there is an output in which the radiation dose emitted at predetermined time intervals is greater than 0 twice or more (S602 / Y), the process proceeds to step S901. In step S 901, the imaging device control unit 118 starts measuring the time from the drive control start time in the timer 1188 at the same time as the drive control unit 1181 starts the drive control, as in the third embodiment.

  Subsequently, in step S902, as in the third embodiment, the imaging device control unit 118 performs a predetermined time after the drive control unit 1181 starts the drive control based on the time measurement of the timer 1188 at the current time. Judge whether or not it has passed. Here, in the present embodiment, the predetermined time is a time X1 required for the radiation irradiation amount shown in FIG. 10 to reach a predetermined value, and the radiation imaging system 10 is installed or regularly maintained, etc. It can be set. If it is determined in step S902 that the predetermined time has not elapsed since the drive control unit 1181 started the drive control (S902 / N), the process waits in step S902.

  On the other hand, if the result of determination in step S902 is that a predetermined time has elapsed since the drive control unit 1181 started drive control (S902 / Y), the process proceeds to step S1102. In step S 1102, the imaging apparatus control unit 118 determines the difference between the radiation doses irradiated at predetermined intervals output from the signal processing unit 117 (for example, the target radiation dose at adjacent predetermined times). It is determined whether or not the difference between the radiation dose at the time and the radiation dose at a predetermined time immediately before that is greater than a predetermined threshold. The predetermined threshold in step S1102 is set to a predetermined threshold B.

  As a result of the determination in step S1102, if the difference between the radiation doses in the adjacent predetermined time is not larger than the predetermined threshold (the difference is equal to or less than the predetermined threshold (difference ≦ predetermined threshold B)) (S1102 / N ), And waits in step S1102. In this case, the imaging device control unit 118 selects the first correction method for correcting the crosstalk component using the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132. If so, the selection is maintained, and thereafter drive control based on the first correction method, crosstalk component correction processing, and the like are performed.

  On the other hand, as a result of the determination in step S1102, if the difference between the radiation doses in the adjacent predetermined time is larger than the predetermined threshold (difference> predetermined threshold B) (S1102 / Y), the process proceeds to step S504. In step S504, the imaging apparatus control unit 118 selects a second correction method for correcting the crosstalk component using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component. Then, the imaging device control unit 118 notifies the drive circuit unit 115, the readout circuit unit 116, the signal processing unit 117, and the like that the second correction method has been selected. Thereafter, the processes of steps S505, S506 and S510 shown in FIG. 5 are performed.

  Then, when the process of step S510 ends, the process of the flowchart illustrated in FIG. 11 ends.

  In the process of the flowchart illustrated in FIG. 11 described above, the imaging device control unit 118 determines whether the difference between the radiation doses at the adjacent predetermined time is larger than the predetermined threshold (S1102). The second correction method (S504, S505) of correcting the crosstalk component using the output signal and the cross using the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132 A process of switching and selecting the first correction method for correcting the talk component is performed. The imaging device control unit 118 that performs this process constitutes a switching unit. According to such a configuration, the second correction method can be selected in the case of imaging with a short irradiation time of radiation that does not allow a long time for correction processing of the crosstalk component. For example, the radiation dose at a predetermined time between the time T1 and the time T2 and the radiation dose at a predetermined time between the time T0 and the time T1 shown in FIG. This is the case where the difference is large). Then, the first correction method can be selected in the case of imaging with a long irradiation time of radiation that is permitted to be long for the crosstalk component correction process. For example, the radiation dose at a predetermined time between time T2 and time T3 and the radiation dose at a predetermined time between time T1 and time T2 immediately before time T3 shown in FIG. This is the case where the difference is small. This makes it possible to correct the crosstalk component appropriately, and as a result, it is also possible to improve the accuracy of the AEC.

Fifth Embodiment
Next, a fifth embodiment of the present invention will be described. In the description of the fifth embodiment described below, the description of matters in common with the first to fourth embodiments described above is omitted, and the matters different from the first to fourth embodiments described above I will explain. Further, in the description of the fifth embodiment described below, configurations and processing steps common to those in the first to fourth embodiments described above are given the same reference numerals for description.

  In the first to fourth embodiments described above, a suitable crosstalk component correction method is switched and selected in accordance with the time related to the process of correcting the crosstalk component. In contrast, the fifth embodiment is a mode in which a suitable crosstalk component correction method is switched and selected according to the degree of freedom of setting in the radiation detection region (ROI). In the fifth embodiment, the first correction method does not use the output signal of the correction pixel 1132 disposed in a fixed manner in the imaging region, so the radiation detection region (ROI) can be freely set. It is a form that focuses on the point that it is possible to do.

  FIG. 12 is a diagram showing an example of a schematic configuration of a radiation imaging system 10 according to a fifth embodiment of the present invention. As illustrated in FIG. 12, the radiation imaging system 10 according to the fifth embodiment is configured to further include a gantry 180 in addition to the configuration illustrated in FIG. 1.

  The gantry 180 is a member on which the radiation imaging apparatus 110 is mounted. In addition, for example, the radiation imaging apparatus 110 is provided with a connector 181 that is a connection unit that can detect attachment to the gantry 180. The radiation imaging apparatus 110 can be attached to and detached from the gantry 180, and radiation imaging (radiography) can be performed in either the state where the radiation imaging device 110 is attached to the gantry 180 or the state where it is detached.

  When the radiation imaging apparatus 110 is attached to the gantry 180 and radiation imaging is performed, since the attachment position is fixed with respect to the gantry 180, alignment at the time of radiation imaging is easy, but the radiation detection area (ROI) The degree of freedom in setting is reduced. On the other hand, when the radiation imaging apparatus 110 is removed from the gantry 180 and radiation imaging is performed, alignment of the subject P1 and the radiation source 162 with the radiation imaging apparatus 110 is difficult, but in the radiation detection region (ROI) The degree of freedom in setting is high, and usability improves.

  FIG. 13 is a flowchart illustrating an example of a processing procedure of a control method in the crosstalk component correction processing by the radiation imaging apparatus 110 according to the fifth embodiment of the present invention.

  First, in step S <b> 1301, the imaging device control unit 118 determines whether the radiation imaging device 110 is mounted on the gantry 180 based on detection by the connector 181.

  If it is determined in step S1301 that the radiation imaging apparatus 110 is mounted on the gantry 180 (S1301 / Y), the process proceeds to step S504. In step S504, the imaging apparatus control unit 118 selects a second correction method for correcting the crosstalk component using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component. Then, the imaging device control unit 118 notifies the drive circuit unit 115, the readout circuit unit 116, the signal processing unit 117, and the like that the second correction method has been selected. Thereafter, the processes of steps S505, S506 and S510 shown in FIG. 5 are performed.

  On the other hand, if it is determined in step S1301 that the radiation imaging apparatus 110 is not mounted on the gantry 180 (S1301 / N), the process proceeds to step S507. In step S507, the imaging device control unit 118 uses the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132 as a correction method for removing the crosstalk component. A first correction method for correcting the component is selected. Then, the imaging apparatus control unit 118 notifies the driving circuit unit 115, the reading circuit unit 116, the signal processing unit 117, and the like that the first correction method has been selected. Thereafter, the processes of steps S508, S509, and S510 shown in FIG. 5 are performed.

  Then, when the process of step S510 ends, the process of the flowchart illustrated in FIG. 13 ends.

  In the process of the flowchart shown in FIG. 13 described above, the imaging device control unit 118 uses the output signal of the correction pixel 1132 according to whether or not the radiation imaging device 110 is attached to the gantry 180 (S1301). A second correction method (S504, S505) for correcting the crosstalk component, and a second correction method for correcting the crosstalk component using the second output signal of the detection pixel 1131 without using the output signal of the correction pixel 1132. A process of switching and selecting one of the correction methods (S507 and S508) is performed. The imaging device control unit 118 that performs this process constitutes a switching unit. According to this configuration, the second correction method is selected when it is assumed that the setting freedom in the radiation detection area (ROI) is low, and the setting freedom in the radiation detection area (ROI) is high. The first correction method can be selected if it is assumed. This makes it possible to correct the crosstalk component appropriately, and as a result, it is also possible to improve the accuracy of the AEC.

<Modification of Fifth Embodiment>
Below, the modification of 5th Embodiment is demonstrated.

  The fifth embodiment of the present invention described above is configured to detect attachment of the gantry 180 to the connector 181 of the radiation imaging apparatus 110 when detecting that the radiation imaging apparatus 110 is attached to the gantry 180. However, the present invention is not limited to this form. For example, a mode in which the radiation imaging apparatus 110 is attached to the gantry 180 is also applicable to the present invention by detecting the external power supply through the gantry 180 by supplying power to the radiation imaging apparatus 110. . Also, for example, if there is a cooling device connected to the radiation imaging apparatus 110 inside the gantry 180, it is detected that the radiation imaging apparatus 110 is attached to the gantry 180 by detecting the connection with the cooling device. The form is also applicable to the present invention.

  In addition, the connection of the radiation imaging apparatus communication cable 170 connected to the communication control device 140 by wire is detected, and the wired connection is detected when the health check signal with the connection destination periodically communicating with the communication control device 140 is interrupted. The radiation imaging apparatus 110 is mounted on the gantry 180 by detecting the disconnection of the link or acquiring the communicable band information from the information at the time of link to determine whether the connection is wired or wireless. The form which detects is also applicable to the present invention. Further, in the case of obtaining and determining communicable band information, it is better to perform control to reduce the amount of communication, such as selecting a crosstalk component correction method with a small number of communication when the communication state is poor.

  Further, according to the first correction method of correcting the crosstalk component without using the output signal of the correction pixel 1132, the correction error is small even when the pixel whose output is largely different in the radiation detection area (ROI) is included. The correction method may be selected focusing on the features that can be used. For example, if the region to be imaged is the lumbar spine, the radiation detection area (ROI) contains pixels with greatly different outputs in the bone and other parts, so in this case the output signal of the correction pixel 1132 is used Instead, it is preferable to select the first correction method for correcting the crosstalk component using the second output signal of the detection pixel 1131.

(Sixth embodiment)
Next, a sixth embodiment of the present invention will be described. In the description of the sixth embodiment described below, the description of matters in common with the first to fifth embodiments described above is omitted, and the matters different from the first to fifth embodiments described above I will explain. Further, in the description of the sixth embodiment described below, configurations and processing steps common to the first to fifth embodiments described above are given the same reference numerals for description.

  In the first to fifth embodiments described above, when the second correction method is performed, the output signal of the correction pixel 1132 is used as another output signal for correcting the first output signal of the detection pixel 1131. Although it was a form to be used, in this invention, it is not limited to this form. For example, an embodiment using an output signal of a wire not connected to the detection pixel 1131 (first pixel) instead of the output signal of the correction pixel 1132 as the other output signal described above is also applicable to the present invention It is. Therefore, this embodiment will be described below as a sixth embodiment of the present invention.

  The schematic configuration of the radiation imaging system according to the sixth embodiment is the same as the schematic configuration of the radiation imaging system 10 according to the first embodiment shown in FIG.

  FIG. 14 is a view showing an example of a schematic configuration of a radiation imaging apparatus 110 according to the sixth embodiment of the present invention. As shown in FIG. 14, the radiation imaging apparatus 110 according to the sixth embodiment has a correction pixel 1132 in the radiation detection unit 113 compared to the configuration of the radiation imaging apparatus 110 according to the first embodiment shown in FIG. 2. Instead of the above, a correction wiring 1136 is provided. In the radiation imaging apparatus 110 according to the sixth embodiment, the readout circuit unit 116 is provided with a detection unit 1164 connected to each of the plurality of correction wirings 1136. The detection unit 1164 reads and detects the output signal of the corresponding correction wiring 1136.

  For example, the correction wiring 1136 illustrated in FIG. 14 is a wiring that is connected to the detection unit 1164 at substantially the same relative position to the column signal line 1135 and the detection pixel 1131 and is not connected to the detection pixel 1131. is there. Then, in the sixth embodiment, when the second correction method for removing the crosstalk component is performed, the above-described first to the other output signals for correcting the first output signal of the detection pixel 1131. Instead of the output signal of the correction pixel 1132 in the fifth embodiment, the output signal of the correction wiring 1136 is used. In the sixth embodiment, when the first correction method for removing the crosstalk component is performed, the first output signal of the detection pixel 1131 as in the first to fifth embodiments described above. Is corrected using the second output signal of the detection pixel 1131.

  According to the sixth embodiment, as in the first embodiment and the like described above, it is possible to correct the crosstalk component appropriately, and as a result, it is also possible to improve the accuracy of the AEC.

(Other embodiments)
The present invention supplies a program that implements one or more functions of the above-described embodiments to a system or apparatus via a network or storage medium, and one or more processors in a computer of the system or apparatus read and execute the program. Can also be realized. It can also be realized by a circuit (for example, ASIC) that realizes one or more functions.
This program and a computer-readable storage medium storing the program are included in the present invention.

  It should be noted that the embodiments of the present invention described above are merely examples of implementation in carrying out the present invention, and the technical scope of the present invention should not be construed as being limited thereto. It is. That is, the present invention can be implemented in various forms without departing from the technical idea or the main features thereof.

110: radiation imaging apparatus, 111: power supply control unit, 113: radiation detection unit, 1131: detection pixel, 1132: correction pixel, 1133: bias line, 1134: drive line, 1135: column signal line, 114: for element Power supply circuit unit, 115: driving circuit unit, 116: readout circuit unit, 1161: detection unit, 1162: multiplexer, 1163: AD conversion unit, 117: signal processing unit, 118: imaging device control unit, 170: radiation imaging Device communication cable

Claims (15)

Radiation detection means configured to include a first pixel for detecting at least any one of detection of irradiation start, detection of irradiation stop, and detection of integrated irradiation amount of the radiation; ,
A first output signal that is an output signal of the first pixel when the output switch of the first pixel is in a conductive state, and a first output signal when the output switch of the first pixel is in a nonconductive state A first correction method of correcting using a second output signal which is an output signal of a pixel, and correcting the first output signal using another output signal different from the second output signal Switching means for switching and selecting the correction method of 2;
What is claimed is: 1. A radiation imaging apparatus comprising: The radiation detecting means further includes a second pixel having a sensitivity different from that of the first pixel to detect the radiation,
The radiation imaging apparatus according to claim 1, wherein the other output signal is an output signal of the second pixel. The radiation detection means further includes a wiring not connected to the first pixel,
The radiation imaging apparatus according to claim 1, wherein the other output signal is an output signal of the wiring.   2. The apparatus according to claim 1, wherein said switching means switches between and selects the first correction method and the second correction method in accordance with the time involved in the process of correcting the first output signal. The radiation imaging device according to any one of 3.   The switching unit selects the second correction method when the irradiation time of the radiation is less than a predetermined threshold, and the first correction method when the irradiation time of the radiation is equal to or more than the predetermined threshold. The radiation imaging apparatus according to any one of claims 1 to 4, wherein   The switching unit selects the second correction method when the radiation dose, which is the amount of the radiation irradiated at predetermined time intervals, is equal to or greater than a predetermined threshold, and the radiation dose is less than the predetermined threshold. The radiation imaging apparatus according to claim 1, wherein the first correction method is selected in some cases.   The switching means selects the second correction method when a predetermined time has not elapsed since the start of driving of the radiation detecting means, and the driving of the radiation detecting means is started, and then the predetermined mode is selected. The radiation imaging apparatus according to claim 1, wherein the first correction method is selected when time has elapsed.   The switching means selects the second correction method when a difference between the radiation doses in a predetermined time adjacent to a radiation dose, which is an amount of the radiation radiated at predetermined time intervals, is larger than a predetermined threshold. The radiation imaging apparatus according to claim 1, wherein the first correction method is selected when the difference is equal to or less than the predetermined threshold value.   4. The method according to claim 1, wherein the switching unit switches and selects the first correction method and the second correction method according to the degree of freedom of setting in the detection region of the radiation. A radiation imaging apparatus according to claim 1.   The switching unit selects the second correction method when the radiation imaging apparatus is mounted on a gantry, and selects the first correction method when the radiation imaging apparatus is not mounted on the gantry. The radiation imaging apparatus according to any one of claims 1 to 3, 9 characterized in that:   When the switching means detects that the radiation imaging apparatus is attached to the gantry, detection of attachment of the gantry to the connection portion of the radiation imaging apparatus, a cooling device provided inside the gantry, and The radiation imaging apparatus according to claim 10, wherein the connection is detected or external power feeding to the radiation imaging apparatus is detected.   4. The apparatus according to any one of claims 1 to 3, wherein the switching unit switches and selects the first correction method and the second correction method according to input information input from an input device. The radiation imaging apparatus according to Item.   The radiation imaging apparatus according to claim 12, further comprising notification means for performing control to notify that effect when the correction method selected according to the input information is not appropriate. The radiation imaging apparatus according to any one of claims 1 to 13.
A radiation generator for generating the radiation;
What is claimed is: 1. A radiation imaging system comprising: Radiation detection means configured to include a first pixel for detecting at least any one of detection of start of irradiation, detection of stop of irradiation and detection of integrated irradiation amount of radiation Detecting using the radiation incident thereon;
A first output signal that is an output signal of the first pixel when the output switch of the first pixel is in a conductive state, and a first output signal when the output switch of the first pixel is in a nonconductive state A first correction method of correcting using a second output signal which is an output signal of a pixel, and correcting the first output signal using another output signal different from the second output signal A switching step of switching and selecting the correction method of 2;
A control method of a radiation imaging apparatus comprising: