Radiation imaging device, radiation imaging system and control method

Abstract

To reduce power consumption during an operation of an AEC function.SOLUTION: A radiation imaging device comprises: imaging means with a plurality of pixel groups including detection pixels for detecting a radiation dose of radiation; a plurality of readout means for reading out signals output from the plurality of pixel groups; and control means, when there is a pixel group that does not include at least one candidate region selected as a region of interest out of a plurality of candidate regions included in an imaging region of the imaging means in the plurality of pixel groups, controlling first readout means to a first state, the first readout means for reading out a signal output from at least one pixel group including at least a part of the at least one candidate region during a detection period for detecting the radiation dose using the detection pixel, and controlling second readout means for reading out a signal output from a pixel group not including the at least one candidate region, to a second state consuming less power than the first state.SELECTED DRAWING: Figure 5

Description

[Technical field]

[0001] The present disclosure relates to a radiation imaging apparatus, a radiation imaging system, and a control method. [Background technology]

[0002] There is known a radiation imaging device having an Automatic Exposure Control (AEC) function, which is a function for measuring the radiation exposure dose using detection pixels of the radiation imaging device and terminating the radiation exposure when the exposure dose reaches a target value.

[0003] Here, Patent Document 1 discloses a radiation imaging device that can reduce power consumption by suppressing the power supplied to a readout circuit that reads out signals output from detection pixels until the AEC function starts operating. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] JP 2019-217198 A Summary of the Invention [Problem to be solved by the invention]

[0005] However, the technology described in Patent Document 1 may not be able to reduce power consumption, for example, while the AEC function is in operation. Therefore, an object of the present disclosure is to reduce power consumption while the AEC function is in operation. [Means for solving the problem]

[0006] The radiation imaging apparatus of the present disclosure includes: an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation; A plurality of readout means for reading out signals output from the plurality of pixel groups; a control means for controlling a first readout means for reading out a signal output from at least one pixel group including at least a part of the at least one candidate region to a first state and a second readout means for reading out a signal output from a pixel group not including the at least one candidate region to a second state consuming less power than the first state during a detection period in which the exposure dose is detected using the detection pixels when the pixel group does not include at least one candidate region selected as a region of interest from among a plurality of candidate regions included in an imaging region of the imaging means, Equipped with. Effect of the Invention

[0007] According to the present disclosure, it is possible to reduce power consumption while the AEC function is in operation. [Brief description of the drawings]

[0008] [Figure 1] 1 is a diagram showing the arrangement of a radiation imaging apparatus according to an embodiment; [Diagram 2] FIG. 2 is a diagram showing the configuration of an amplifier according to the embodiment. [Diagram 3] FIG. 2 is a plan view showing the configuration of each pixel according to the embodiment. [Figure 4] FIG. 2 is a cross-sectional view showing the configuration of each pixel according to the embodiment. [Diagram 5] FIG. 1 is a diagram showing an example of the arrangement of a radiation imaging system according to an embodiment. [Figure 6] 4 is a diagram showing an example of the operation of the radiation imaging system according to the embodiment; [Figure 7] FIG. 4 is a diagram showing a GUI according to the embodiment. [Figure 8] 5A and 5B are diagrams showing the correspondence between candidate areas and readout circuits according to the embodiment. [Figure 9] 4 is a diagram showing a shooting flow by an operator and an operation flow of a control unit 180 according to the embodiment. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0009] The embodiments of the present disclosure will be described below with reference to the accompanying drawings. Similar elements throughout the various embodiments are designated by the same reference numerals, and duplicated descriptions will be omitted. In addition, each embodiment can be appropriately modified and combined.

[0010] 5 shows an example of the configuration of a radiation imaging system 500 including the radiation imaging device 100. The radiation imaging system 500 includes the radiation imaging device 100, an information processing device 502, an access point 503, a communication device 504, a synchronization control device 505, a radiation generation device 506, an in-hospital LAN 508, and a status notification device 509.

[0011] The radiation imaging device 100 captures a radiation image based on radiation 507 that has passed through the subject H. The radiation image captured by the radiation imaging device 100 is sent to an information processing device 502.

[0012] The information processing device 502 is a control device realized by a known technology such as a general-purpose computer. The information processing device 502 is communicably connected to the radiation imaging device 100 via the access point 503. The information processing device 502 performs image processing for correction, storage, and display of a radiation image received from the radiation imaging device 100. At this time, a part or all of the functions of the image processing may be performed by the radiation imaging device 100. The information processing device 502 also has a display control unit 511, and performs display control such as displaying a radiation image to an operator and displaying a GUI to the operator through a display unit 510 such as a display. The display control unit 511 is an example of a display control means. The information processing device 502 also has an input unit (not shown), and imaging conditions and the like instructed by the operator are input to the input unit. The information processing device 502 also compares a signal intensity acquired from the access point 503 or the like with a threshold value. The information processing device 502 also responds to a connection request from the access point 503 or the like. The information processing device 502 also has a function of transmitting wireless information for communication by the wireless communication unit to the access point 503 or the like.

[0013] The access point 503 is a device that relays radio waves for wirelessly exchanging information between the radiation imaging apparatus 100 and the information processing apparatus 502. Note that, although the access point 503 is connected to the information processing apparatus 502 via the synchronization control device 505 in Fig. 5, it may be directly connected to the information processing apparatus 502.

[0014] The communication device 504 is connected to the information processing device 502 and is a device that transmits and receives radio waves for wireless short-distance communication between the radiation imaging apparatus 100 and the information processing device 502. For example, the communication device 504 is a dongle that is connected to the information processing device 502 via a Universal Serial Bus (USB) interface. For example, the communication device 504 is a device that complies with at least one of the Bluetooth (registered trademark) Basic Rate / Enhanced Data Rate (BR / EDR) standard and the Bluetooth Low Energy (BLE) standard. The communication device 504 may be an RFID (radio frequency IDentifier) ​​device that exchanges information from a tag in which ID information is embedded by short-distance wireless communication using an electromagnetic field, radio waves, or the like. The communication method of RFID may be an electromagnetic induction method or a radio wave method. The communication device 504 may have a function of an access point.

[0015] 5, an example in which the communication device 504 is connected to the information processing device 502 is shown, but this is not limiting. The communication device 504 may be connected to other devices constituting the radiation imaging system 500, such as a radiation generating device 506. The communication device 504 does not necessarily have to be an independent device. For example, the communication device 504 may be a device incorporated in any of the devices constituting the radiation imaging system 500.

[0016] The status notification device 509 is connected to the information processing device 502. The status notification device 509 is a means for notifying the operator. The status notification device 509 notifies the operator of the current status of the radiation imaging apparatus 100 or the completion of a specific process based on information of the radiation imaging apparatus 100 received via the access point 503 or the communication device 504. The status notification device 509 uses, for example, a light-emitting body such as an LED. The status notification device 509 notifies the operator by previously associating a plurality of lighting patterns with a plurality of states of the radiation imaging apparatus 100. The status notification device 509 may also use a sound source such as a speaker. In that case, the status notification device 509 notifies the operator by previously associating a plurality of buzzer sound patterns with a plurality of states of the radiation imaging apparatus 100. The status notification device 509 may also be a device in which a light-emitting body and a sound source are combined. Although an example in which the status notification device 509 is connected to the information processing device 502 has been shown, a display, a speaker, or the like built into the information processing device 502 may also be used.

[0017] The synchronization control device 505 has a circuit that mediates communication and monitors the states of the radiation imaging apparatus 100 and the radiation generation apparatus 506. For example, the synchronization control device 505 controls the emission of radiation 507 from the radiation generation apparatus 506 and controls the imaging of the subject H by the radiation imaging apparatus 100. The synchronization control device 505 may also include a built-in hub that connects multiple network devices.

[0018] The radiation generating device 506 is a device that generates radiation 507 such as X-rays. The radiation generating device 506 has, for example, a radiation tube that accelerates electrons with a high voltage and causes them to collide with an anode. Note that, in addition to X-rays, α-rays, β-rays, γ-rays, and neutron rays may be used as the radiation 507. The radiation 507 emitted from the radiation generating device 506 is irradiated onto a subject H who is a patient.

[0019] The hospital LAN 508 is a local area network established within the hospital, and has a function of transmitting and receiving radiation images captured by the radiation imaging system 500 to and from each location within the hospital.

[0020] Here, the radiation imaging system 500 can perform imaging by two methods, namely, synchronous imaging and asynchronous imaging. Synchronous imaging is an imaging method in which the timing of radiation irradiation and imaging is synchronized by exchanging an electrical synchronization signal between the radiation imaging apparatus 100 and the radiation generation apparatus 506 via a synchronization control device 505. On the other hand, asynchronous imaging is an imaging method in which the radiation imaging apparatus 100 starts imaging by detecting incidence of radiation without exchanging an electrical synchronization signal between the radiation imaging apparatus 100 and the radiation generation apparatus 506. In asynchronous imaging, the radiation imaging apparatus 100 may transfer a radiation image for each imaging, or may store the captured image inside the radiation imaging apparatus 100 without transferring the image for each imaging.

[0021] In addition, the radiation imaging system 500 can perform imaging under imaging conditions commonly used in radiation imaging, such as fluoroscopic imaging, continuous imaging, still image imaging, DSA imaging, roadmap imaging, program imaging, tomography imaging, and tomosynthesis imaging.

[0022] Further, in the radiation imaging system 500, various function settings are made, such as an imaging frame rate, a tube voltage, a tube current, a sensor readout area, a sensor drive binning setting, a collimator aperture setting, a radiation window width, and whether or not to store radiation images in the radiation imaging device 100. In addition, in the radiation imaging system 500, functions such as an automatic dose control (ADC) and an automatic exposure control (AEC) are set.

[0023] 1A is a schematic configuration example of a radiation imaging device 100 according to an embodiment of the present disclosure. The radiation imaging device 100 includes an imaging region IR, a power supply circuit 140 that supplies power to the imaging region IR, a drive circuit 150 for driving the imaging region IR, a readout circuit 160 that reads out a signal imaged in the imaging region IR, a signal processing unit 170 that processes the signal read out by the readout circuit 160, a control unit 180 that controls the drive circuit 150, the readout circuit 160, and the signal processing unit 170, and a communication unit 190.

[0024] The imaging region IR is made up of imaging regions IR(1) to (5). The boundaries between the imaging regions IR(1) to (5) are indicated by dashed lines. Each imaging region IR includes imaging pixels, which will be described later. Each imaging region IR may include detection pixels, which will be described later, in addition to the imaging pixels. The imaging region IR is, for example, a planar detector formed from a semiconductor material. The imaging region IR(1) and the imaging region IR(2) are examples of pixel groups. The imaging region IR made up of the imaging regions IR(1) to (5) is an example of an imaging means.

[0025] The readout circuit 160 is made up of readout circuits (1) to (5). The boundaries between the readout circuits (1) to (5) are indicated by dashed lines. Signals output from the imaging regions IR(1) to (5) are read out by the readout circuits (1) to (5). For example, the region IR(1) is read out by the readout circuit (1). Furthermore, for example, the region IR(2) is read out by the readout circuit (2). Each of the readout circuits (1) to (5) is composed of an electrical component such as an IC (Integrated Circuit) chip. The readout circuits (1) and (2) are examples of a readout means.

[0026] A region of interest can be set in the imaging region IR. The region of interest is an area that is mainly used by a doctor for diagnosis. The region of interest is selected from predefined candidate regions (R1 to R9). Before imaging, the doctor or operator selects one of the candidate regions (R1 to R9) as the region of interest. The candidate regions (R1 to R9) include imaging pixels and detection pixels, which will be described later.

[0027] The signal processing unit 170 includes a calculation unit 171 and a storage unit 172. The signal processing unit 170 receives the signals read out from the readout circuits (1) to (5) and performs signal processing such as calculation and storage on the signals.

[0028] The communication unit 190 is controlled by the control unit 180 and has a function of communicating between the radiation imaging apparatus 100 and an external device. The communication is not limited to a specific standard and may be realized by using the communication unit 190 that realizes communication of a desired method or standard, such as wired communication or wireless communication. Furthermore, a plurality of communication units 190 may be installed to support a plurality of communication standards.

[0029] Fig. 1(b) shows a detailed configuration example of the radiation imaging device 100 according to the embodiment of the present disclosure. Fig. 1(b) is a diagram showing the part enclosed by the dashed line in Fig. 1(a). The radiation imaging device 100 has a plurality of pixels arranged in an imaging region IR to form a plurality of rows and a plurality of columns, a plurality of driving lines 110, and a plurality of signal lines 120. The plurality of driving lines 110 are arranged corresponding to a plurality of rows of pixels, and each driving line 110 corresponds to one of the pixel rows. The plurality of signal lines 120 are arranged corresponding to a plurality of columns of pixels, and each signal line 120 corresponds to one of the pixel columns.

[0030] The plurality of pixels include a plurality of imaging pixels 101 used to acquire a radiation image, one or more detection pixels 104 used to detect an exposure dose of radiation, and one or more correction pixels 107 used to correct the exposure dose of radiation. The sensitivity of the correction pixels 107 to radiation is lower than the sensitivity of the detection pixels 104 to radiation.

[0031] The imaging pixel 101 includes a conversion element 102 that converts radiation into an electric signal, and a switch element 103 that connects the corresponding signal line 120 and the conversion element 102 to each other. The detection pixel 104 includes a conversion element 105 that converts radiation into an electric signal, and a switch element 106 that connects the corresponding signal line 120 and the conversion element 105 to each other. The detection pixel 104 is arranged so as to be included in a row and a column formed by a plurality of imaging pixels 101. The correction pixel 107 includes a conversion element 108 that converts radiation into an electric signal, and a switch element 109 that connects the signal line 120 and the conversion element 108 to each other. The correction pixel 107 is arranged so as to be included in a row and a column formed by a plurality of imaging pixels 101. In FIG. 1 and subsequent drawings, the imaging pixel 101, the detection pixel 104, and the correction pixel 107 are distinguished from each other by applying different hatching to the conversion element 102, the conversion element 105, and the conversion element 108.

[0032] The conversion element 102, the conversion element 105, and the conversion element 108 may be composed of a scintillator that converts radiation into light, and a photoelectric conversion element that converts light into an electrical signal. The scintillator is generally formed in a sheet shape so as to cover the imaging region IR, and is shared by a plurality of pixels. Alternatively, the conversion element 102, the conversion element 105, and the conversion element 108 may be composed of a conversion element that directly converts radiation into an electrical signal.

[0033] The switch element 103, the switch element 106, and the switch element 109 may each include a thin film transistor (TFT) having an active region made of a semiconductor such as amorphous silicon or polycrystalline silicon.

[0034] A first electrode of the conversion element 102 is connected to a first main electrode of the switch element 103, and a second electrode of the conversion element 102 is connected to a bias line 130. One bias line 130 extends in the column direction and is commonly connected to second electrodes of a plurality of conversion elements 102 arranged in the column direction. The bias line 130 receives a bias voltage Vs from a power supply circuit 140. Second main electrodes of the switch elements 103 of one or more imaging pixels 101 included in one column are connected to one signal line 120. Control electrodes of the switch elements 103 of one or more imaging pixels 101 included in one row are connected to one drive line 110.

[0035] The detection pixel 104 and the correction pixel 107 also have the same pixel configuration as the imaging pixel 101, and are connected to the corresponding drive line 110 and the corresponding signal line 120. The detection pixel 104 and the correction pixel 107 are exclusively connected to the signal line 120. That is, the correction pixel 107 is not connected to the signal line 120 to which the detection pixel 104 is connected. Furthermore, the detection pixel 104 is not connected to the signal line 120 to which the correction pixel 107 is connected. The imaging pixel 101 may be connected to the same signal line 120 as the detection pixel 104 or the correction pixel 107.

[0036] The driving circuit 150 is configured to supply driving signals to the pixels to be driven through the multiple driving lines 110 according to a signal from the control unit 180. In this embodiment, the driving signal is a signal for turning on a switch element included in the pixel to be driven. The switch element of each pixel is turned on by a high-level signal and turned off by a low-level signal. Therefore, this high-level signal is called a driving signal. By supplying the driving signal to the pixel, the signal accumulated in the conversion element of this pixel becomes readable by the readout circuit 160. When the driving line 110 is connected to at least one of the detection pixel 104 and the correction pixel 107, the driving line 110 is called a detection driving line 111.

[0037] The readout circuit 160 is configured to read out signals from a plurality of pixels through a plurality of signal lines 120. The readout circuit 160 includes a plurality of amplifiers 161, a multiplexer 162, and an analog-to-digital converter (hereinafter, AD converter) 163. Each of the plurality of signal lines 120 is connected to a corresponding one of the plurality of amplifiers 161 in the readout circuit 160. One signal line 120 corresponds to one amplifier 161. The multiplexer 162 selects the plurality of amplifiers 161 in a predetermined order, and supplies a signal from the selected amplifier 161 to the AD converter 163. The AD converter 163 converts the supplied signal into a digital signal and outputs it.

[0038] The signals read out from the imaging pixels 101 are supplied to the signal processing unit 170, which performs processing such as calculation and storage. Specifically, the signal processing unit 170 includes a calculation unit 171 and a storage unit 172. The calculation unit 171 generates a radiographic image based on the signals read out from the imaging pixels 101 and supplies the generated radiographic image to the control unit 180. The signals read out from the detection pixels 104 and the correction pixels 107 are supplied to the signal processing unit 170, which performs processing such as calculation and storage. Specifically, the signal processing unit 170 outputs information indicating irradiation of radiation to the radiation imaging device 100, based on the signals read out from the detection pixels 104 and the correction pixels 107. For example, the signal processing unit 170 detects irradiation of radiation to the radiation imaging device 100, and determines the irradiation amount and / or irradiation dose (accumulated irradiation amount) of radiation.

[0039] The control unit 180 controls the drive circuit 150 and the readout circuit 160 based on information from the signal processing unit 170. The control unit 180 controls, for example, the start and end of exposure (accumulation of electric charges corresponding to irradiated radiation by the imaging pixels 101) based on information from the signal processing unit 170. The control unit 180 may be configured with a general-purpose processing circuit such as a microprocessor, or may be configured with a dedicated processing circuit such as an ASIC (Application Specific Integrated Circuit). When the control unit 180 is configured with a general-purpose processing circuit, the control unit 180 may further include a memory. Note that the control unit 180 is an example of a control means.

[0040] In order to determine the radiation exposure dose, the control unit 180 controls the drive circuit 150 to scan only the detection drive lines 111 and to make it possible to read out only signals from the detection pixels 104 and the correction pixels 107. Next, the control unit 180 controls the readout circuit 160 to read out signals from columns corresponding to the detection pixels 104 and the correction pixels 107 and output them as information indicating the radiation exposure dose. Through such an operation, the radiation imaging device 100 can obtain irradiation information on the detection pixels 104 during radiation exposure.

[0041] 2 shows a detailed circuit configuration example of the amplifier unit 161. The amplifier unit 161 includes a differential amplifier circuit AMP and a sample-and-hold circuit SH. The differential amplifier circuit AMP amplifies and outputs a signal appearing on the signal line 120. The control unit 180 can reset the potential of the signal line 120 by supplying a signal φR to the switch element of the differential amplifier circuit AMP. The output from the differential amplifier circuit AMP can be held by the sample-and-hold circuit SH. The control unit 180 causes the sample-and-hold circuit SH to hold the signal by supplying a signal φSH to the switch element of the sample-and-hold circuit SH. The signal held in the sample-and-hold circuit SH is read out by the multiplexer 162.

[0042] An example of the structure of pixels of the radiation imaging device 100 will be described with reference to Fig. 3 and Fig. 4. Fig. 3 is a plan view showing the configurations of the imaging pixels 101, detection pixels 104, and correction pixels 107 in the radiation imaging device 100. The plan view is equivalent to an orthogonal projection onto a plane parallel to the imaging region IR of the radiation imaging device 100. As indicated by hatching, a metal layer is disposed on the conversion element 108 of the correction pixel 107, and the conversion element 108 is shielded from light by this metal layer.

[0043] FIG. 4(a) is a cross-sectional view of the imaging pixel 101 taken along line A-A' in FIG. 3. The cross-sectional view of the detection pixel 104 is similar to the cross-sectional view of the imaging pixel 101. The switch element 103 is disposed on an insulating support substrate 400 such as a glass substrate. The switch element 103 may be a TFT (thin film transistor). An interlayer insulating layer 401 is disposed on the switch element 103. The conversion element 102 is disposed on the interlayer insulating layer 401. The conversion element 102 is a photoelectric conversion element capable of converting light into an electric signal. The conversion element 102 is composed of, for example, an electrode 402, a PIN photodiode 403, and an electrode 404. The conversion element 102 may be composed of an MIS type sensor instead of a PIN type photodiode.

[0044] A protective film 405, an interlayer insulating layer 406, a bias line 130, and a protective film 407 are disposed in this order on the conversion element 102. A planarizing film and a scintillator (not shown) are disposed on the protective film 407. The electrode 404 is connected to the bias line 130 via a contact hole. ITO having optical transparency is used as the material of the electrode 404, and it is possible for light converted from radiation by the scintillator (not shown) to pass through it.

[0045] 4(b) is a cross-sectional view of the correction pixel 107 taken along line B-B' in FIG. 3. The correction pixel 107 differs from the imaging pixel 101 and the detection pixel 104 in that the conversion element 108 is covered with a light-shielding member 408, but may be the same in other respects. The light-shielding member 408 is formed, for example, from the same metal layer as the bias line 130. Since the conversion element 108 of the correction pixel 107 is covered with the light-shielding member 408, the sensitivity of the correction pixel 107 to radiation is significantly lower than the sensitivity of the imaging pixel 101 and the detection pixel 104. In other words, the charge accumulated in the conversion element 108 of the correction pixel 107 is hardly affected by radiation.

[0046] The imaging flow by the operator and the operational flow of the control unit 180 will be described with reference to FIG.

[0047] In S901, the operator uses the GUI displayed on the display unit 510 to select an imaging technique.

[0048] FIG. 7 shows an example of the GUI displayed on the display unit 510. As shown in FIG.

[0049] In the GUI shown in FIG. 7(a), a selection section 701 for selecting an imaging technique and a schematic diagram 702 showing the positions of candidate regions R1 to R9 in the radiation imaging apparatus 100 are displayed.

[0050] The operator uses the selection unit 701 to select a desired imaging technique from among a plurality of options. When the imaging technique is selected, a region of interest to be used for AEC imaging is selected from the candidate regions R1 to R9. For example, when a cardiac imaging technique is selected, R5 is selected as the region of interest. That is, R5 is selected as the region of interest by an instruction from the operator. The schematic diagram 702 shows an example in which the selected R5 is displayed in an emphasized manner. Here, the region of interest may be selected in association with the imaging technique, or may be selected individually by the operator.

[0051] In addition, the GUI shown in FIG. 7(b) displays a selection region 703 for selecting a setting pattern for a region of interest, and a schematic diagram 702 showing the positions of candidate regions R1 to R9 in the radiation imaging apparatus 100.

[0052] The operator selects one of the multiple setting patterns displayed in the selection area 703. When a setting pattern is selected, the region of interest to be used in AEC imaging is selected based on the selected setting pattern. For example, when the operator selects the setting pattern on the lower left with the mouse cursor 704, R5, R7, and R9 are selected as the region of interest.

[0053] When a region of interest is selected by an instruction from an operator, power control of the readout circuit during charge readout performed in S912 is determined in association with the selected region of interest. Here, the GUI may be capable of inputting not only the selection of an imaging technique but also the dose, the upper limit of irradiation time (ms), the tube current (mA), and the tube voltage (kV).

[0054] When an imaging technique is selected, the operator performs alignment between the radiation tube, the subject, and the radiation imaging device in S902. For example, when a cardiac imaging technique is selected in S901, R5 is selected as the region of interest, so the operator performs alignment so that the position of the patient's heart is the position of R5.

[0055] When an imaging technique is selected, the control unit 180 performs a charge reset operation (S911). At this time, the control unit 180 operates all readout circuits in a mode with low power consumption (low power consumption mode). After the charge reset operation, the control unit 180 starts a charge readout operation (S912). At this time, the control unit 180 changes the operation mode of the readout circuit that reads out signals output from a pixel group including a candidate region selected as a region of interest. For example, when a cardiac imaging technique is selected in S901, R5 is selected as a region of interest, so the control unit 180 changes the operation mode of the readout circuit (2) and the readout circuit (3). Specifically, the control unit 180 changes from the low power consumption mode to a readout mode for reading out charges. The change of the operation mode may be, for example, by changing the config setting value (setting value for IC) of the readout circuit, or may change the voltage and current. For example, when changing the voltage, the voltage supplied to the readout circuit is increased from a GND voltage (for example, 0 V) ​​to an operating voltage (for example, 1.8 V). The readout circuit (2) and the readout circuit (3) are an example of a first readout means. The readout circuit (1), the readout circuit (4), and the readout circuit (5) other than the readout circuit (2) and the readout circuit (3) are an example of a second readout means. The readout mode for reading out electric charges is an example of a first state. The low power consumption mode is an example of a second state. The operating voltage is an example of a first voltage. The GND voltage is an example of a second voltage lower than the first voltage. The imaging regions IR(1), (4), and (5) that do not include R5 selected as a region of interest are an example of a pixel group that does not include at least one candidate region selected as a region of interest.

[0056] Furthermore, if there is a pixel group that does not include R5 selected as the region of interest, the pixel group is left in a low power consumption mode (low power consumption mode). Specifically, readout circuits other than readout circuit (2) and readout circuit (3) do not include R5 selected as the region of interest, so they are left in the low power consumption mode.

[0057] By performing the above-mentioned operations, the readout circuits other than the readout circuit (2) and the readout circuit (3) can be operated in a low power consumption mode (low power consumption mode), thereby reducing the power consumption.

[0058] Here, the control unit 180 can improve the correction accuracy by acquiring correction information for correcting the charge read out in S912 before S911 and performing correction using the acquired correction information. Furthermore, accuracy can be improved by setting the power consumption mode of the readout circuit when acquiring this correction information to be the same as the power consumption mode of S912. Note that the correction information for correcting the charge is an example of first correction data for correcting the irradiation dose. Also, the period before S911 when the correction information is acquired is an example of the first period.

[0059] When S902 ends, the operator starts irradiation of radiation in S903. Specifically, for example, the operator operates an exposure switch attached to the radiation generation device 506. When the exposure switch is operated, the information processing device 502 transmits a start request signal to the radiation imaging device 100. The start request signal is a signal requesting to start preparations to receive irradiation of radiation. In response to receiving the start request signal, the radiation imaging device 100 starts preparations to receive irradiation of radiation. When preparations are complete, the radiation imaging device 100 transmits a start possible signal to the radiation generation device 506 via the access point 503 or the communication device 504. The start possible signal is a signal notifying that irradiation of radiation can be started. In response to receiving the start possible signal, the radiation generation device 506 starts irradiation of radiation 507.

[0060] When irradiation of the radiation 507 is started, the amount of charge read out in the charge readout in S912 increases. When a certain amount of charge or more is read out, the control unit 180 notifies the radiation stop in S913. Specifically, when the control unit 180 reaches a threshold of the integrated value of the dose of the irradiated radiation, it transmits an irradiation stop signal to the radiation generating device 506 via the access point 503 or the communication device 504. The irradiation stop signal is a signal requesting the end of irradiation of radiation. In response to receiving the irradiation stop signal, the radiation generating device 506 ends the irradiation of the radiation 507. The dose threshold is determined based on the input value of the dose, the radiation irradiation intensity, the communication delay between each unit, the processing delay, and the like. When the irradiation time of the radiation reaches the input upper irradiation limit time, the radiation generating device 506 may stop the irradiation of the radiation even if it has not received the irradiation stop signal. Note that the period from S912, when the charge reading operation is started, to S913, when the radiation stop is notified, is an example of a detection period.

[0061] When the irradiation of radiation is stopped, the operator confirms that the irradiation of radiation has been stopped in S904. Specifically, for example, the operator confirms the display of the GUI.

[0062] Furthermore, when the irradiation of radiation is stopped, the control unit 180 reads out the radiographic image in S914. Note that the period during which S914 for reading out the radiographic image is executed is an example of an image acquisition period.

[0063] Thereafter, in S915, the control unit 180 resets the electric charges in order to correct the radiation image read out in S914.

[0064] Next, the control unit 180 performs a charge read operation in S916. Furthermore, next, the control unit 180 performs an image read operation in S917. The control unit 180 performs correction of the radiographic image read in S914 using the charge read in S916 and the image read in S917. Furthermore, the control unit 180 transfers the corrected radiographic image to the information processing device 502 using wired or wireless communication. Note that the image used for correction may be one prepared in advance. In addition, in the charge read operation performed in S916, it is possible to improve the correction accuracy by setting the power supply state of the readout circuit to the same state as in S912. Note that the charge read in S916 and the image read in S917 are examples of second correction data for correcting the radiographic image. Also, the period during which S916 and S917 are performed is an example of a second period.

[0065] When the corrected radiation image is transferred to the information processing device 502, the operator checks the transferred radiation image in S905.

[0066] The operations of S911 to S914 of the control unit 180 will be described in further detail with reference to the timing chart of Fig. 6. These operations are executed by cooperation between the control unit 180, which controls the drive circuit 150 and readout circuit 160, and the signal processing unit 170. The amount of radiation irradiated to the radiation imaging device 100 is determined by these operations.

[0067] First, the legend will be explained. The "start request signal", "start enable signal", and "irradiation stop signal" have been described above, so their explanation will be omitted. "Radiation" indicates whether radiation is being irradiated to the radiation imaging device 100. When it is low, radiation is not being irradiated, and when it is high, radiation is being irradiated. "Vg1" to "Vgn" indicate drive signals supplied from the drive circuit 150 to the multiple drive lines 110. "Vgk" corresponds to the drive line 110 in the kth row (k=1, ..., total number of drive lines). As described above, some of the multiple drive lines 110 are also called detection drive lines 111. The jth detection drive line 111 is represented as "Vdj" (j=1, ..., total number of detection drive lines).

[0068] φSH indicates the level of the signal supplied to the sample-and-hold circuit SH of the amplifier 161. φR indicates the level of the signal supplied to the differential amplifier circuit AMP of the amplifier 161. "Detection pixel signal" indicates the value of the signal read out from the detection pixel 104. "Correction pixel signal" indicates the value of the signal read out from the correction pixel 107. "Exposure dose (accumulated exposure dose)" indicates the accumulated value of radiation irradiated to the radiation imaging device 100. A method for determining this accumulated value will be described later.

[0069] Next, the operation of the control unit 180 from time t0 to t10 will be described.

[0070] At time t0, the control unit 180 starts a reset operation of a plurality of pixels. The reset operation is an operation of removing the electric charge accumulated in the conversion element of each pixel. Specifically, the electric charge is removed by supplying a drive signal to the drive line 110 and turning on the switch element of each pixel. The control unit 180 resets each pixel connected to the drive line 110 of the first row by controlling the drive circuit 150. Then, the control unit 180 resets each pixel connected to the drive line 110 of the second row. The control unit 180 repeats this operation up to the drive line 110 of the last row. At time t1, the control unit 180 finishes the reset operation of the drive line 110 of the last row, and then repeats the reset operation again from the drive line 110 of the first row.

[0071] At time t2, the control unit 180 receives a start request signal from the information processing device 502. In response to receiving the start request signal, the control unit 180 performs the reset operation up to the last row and ends the reset operation. The control unit 180 may end the reset operation before performing the reset operation up to the last row and move on to the next process. For example, when the control unit 180 receives the start request signal during the reset operation of the kth row of the drive line 110, the control unit 180 may move on to the next process without performing the reset operation of the drive line 110 of the k+1th row and onwards. In this case, a step that may occur in the radiographic image may be reduced by adjusting the drive for acquiring the radiographic image or performing image processing on the radiographic image.

[0072] At time t3, the control unit 180 starts a determination operation for determining the amount of radiation being irradiated to the radiation imaging device 100. In the determination operation, the control unit 180 repeatedly executes a read operation to read from the detection pixel 104 and the correction pixel 107. Among the multiple read operations repeatedly executed, one or more read operations executed in the first half are executed to determine a correction value. In addition, one or more read operations executed in the second half are executed to continuously determine the amount of radiation at each time point. The read operation is executed for the detection drive line 111, and is not executed for the other drive lines 110. Specifically, the drive circuit 150 supplies a drive signal to the drive line 110 (i.e., the detection drive line 111) connected to at least one of the detection pixel 104 and the correction pixel 107 among the multiple drive lines 110. However, the drive circuit 150 does not supply a drive signal to the drive line 110 not connected to either the detection pixel 104 or the correction pixel 107 among the multiple drive lines 110. Furthermore, the drive circuit 150 simultaneously supplies drive signals to the drive lines 110 connected to at least one of the detection pixel 104 and the correction pixel 107 among the multiple drive lines 110. As a result, signals from multiple pixels connected to the same signal line 120 are combined and read out to the readout circuit 160. Since the detection pixel 104 and the correction pixel 107 are exclusively connected to the signal line 120, the readout circuit 160 can separately read out signals from pixels with different sensitivities.

[0073] The above operation from time t0 to time t3 corresponds to S911 in FIG.

[0074] In one readout operation, the control unit 180 performs an operation from time t3 to time t4. Specifically, the control unit 180 temporarily supplies a drive signal to one or more detection drive lines 111. After that, the control unit 180 holds in the sample-and-hold circuit SH the signal read out from the pixel through the signal line 120 to the readout circuit 160 by temporarily setting the signal φSH to a high level. After that, the control unit 180 resets the readout circuit 160 (specifically, the differential amplifier circuit AMP of the amplifier unit 161) by temporarily setting the signal φR to a high level. When a region of interest is set within the imaging region IR, it is not necessary to read out signals from the detection pixels 104 that are not included in this region of interest.

[0075] The control unit 180 performs a read operation a predetermined number of times to determine the correction value. The signal processing unit 170 determines a correction value Od based on the signal read from the detection pixel 104 and a correction value Oc based on the signal read from the correction pixel 107 by the read operation performed a predetermined number of times.

[0076] The determination of the correction value Od will be described in detail. When the predetermined number of times is one, one signal is read from the detection pixel 104, and the signal processing unit 170 sets the value of that signal as the correction value Od. When the predetermined number of times is multiple, the signal processing unit 170 sets the average value of the multiple read signals as the correction value Od. Other statistical values ​​may be used instead of the average value. The correction value Oc is also determined in the same manner based on the signal read from the correction pixel 107. The signal processing unit 170 stores the correction values ​​Od and Oc determined in this manner in the memory unit 172, making them available for subsequent processing.

[0077] After completing one or more read operations, the control unit 180 transmits a start possible signal to the radiation generating device 506 at time t5. The above-mentioned correction values ​​Od and Oc may be determined before or after the start possible signal is transmitted. After transmitting the start possible signal, the control unit 180 repeatedly executes the above-mentioned read operation. The signal processing unit 170 measures the amount of radiation irradiation for each read operation and determines whether or not the accumulated value of the irradiation amount exceeds a threshold value. Here, the irradiation amount is a value read out in one read operation. Also, the accumulated value of the irradiation amount is a value obtained by accumulating the irradiation amounts read out multiple times. Also, in this embodiment, the accumulated value of the irradiation amount is also referred to as the irradiation dose (accumulated irradiation amount). Radiation irradiation is started at time t6 after time t5.

[0078] When the irradiation dose (accumulated irradiation dose) reaches the threshold at time t8, the control unit 180 transmits an irradiation stop signal to the synchronization control device 505. The synchronization control device 505 receives the irradiation stop signal and controls the radiation irradiation stop of the radiation generation device 506. Here, the control unit 180 may estimate the time t8 (predicted arrival time) at which the irradiation dose (accumulated irradiation dose) reaches the threshold, and further calculate an estimated transmission time t7 by adding a communication delay time from the communication unit 190 until a signal reaches the synchronization control device 505 to the predicted arrival time, and transmit the irradiation stop signal at this estimated transmission time t7.

[0079] The above operation from time t3 to time t8 corresponds to S912 to S913 in Fig. 9. The period from time t3 to time t8 is an example of a detection period.

[0080] At time t9, the radiation generation device 506 stops the radiation irradiation in response to the irradiation stop control from the synchronization control device 505.

[0081] When the irradiation of radiation is completed at time t9, the control unit 180 causes the radiation imaging device 100 to sequentially scan the driving lines 110 (the driving lines 110 other than the detection driving lines 111) to which only the imaging pixels 101 are connected, and the image signals of each imaging pixel 101 are read out by the readout circuit 160, thereby acquiring a radiation image. Here, since the charge accumulated in the detection pixel 104 is read out during irradiation of radiation and the correction pixel 107 is shielded from light, the signals from these pixels cannot be used to form a radiation image. Therefore, the signal processing unit 170 of the radiation imaging device 100 performs an interpolation process using the pixel values ​​of the imaging pixels 101 around the detection pixel 104 and the correction pixel 107, thereby interpolating the pixel values ​​at the positions of these pixels. After the acquisition of the radiation image is completed at time t10, the control unit 180 performs a reset operation of a plurality of pixels from time t10 in the same manner as at times t0 to t3.

[0082] The above operation from time t9 to time t10 corresponds to S914 in Fig. 9. The period from time t9 to time t10 is an example of an image acquisition period.

[0083] The detailed operation of the control unit 180 has been described above.

[0084] Here, in the configuration of FIG. 1(a), when R5 is selected as the region of interest, the readout circuits (2) and (3) are put into readout mode. Therefore, for example, by changing the correspondence between the candidate region and the readout circuit as shown in FIG. 8(a), the power consumption can be further reduced. In FIG. 8, the boundary (dashed line) between the candidate region and the readout circuit is made to coincide. In this correspondence, the imaging region IR(2) including the detection pixel is read out by the readout circuit (2). Similarly, the imaging region IR(4) including the detection pixel is read out by the readout circuit (4). Moreover, the imaging region IR(1) not including the detection pixel is read out by the readout circuit (1). Similarly, the imaging region IR(3) not including the detection pixel is read out by the readout circuit (3). By making this correspondence, for example, when R5 is selected as the region of interest, only the readout circuit (4) needs to be put into readout mode during the period (detection period) from S912, when the charge readout operation is started, to S913, when the radiation stop is notified. That is, the readout circuits other than the readout circuit (4) can be kept in a low power consumption mode (low power consumption mode). As a result, for example, power consumption can be further reduced compared to FIG. 1(a). Note that the imaging regions IR(1), (3), (5), and (7) that do not include detection pixels are an example of a plurality of second pixel groups that do not include detection pixels. Also, the readout circuits (1), (3), (5), and (7) are an example of a third readout means.

[0085] Moreover, power consumption can be further reduced by changing the correspondence between the candidate regions and the readout circuits as shown in Fig. 8(b). In Fig. 8(b), IRs (1), (3), (5), and (7) that do not correspond to the candidate regions are read out by one readout circuit (1). By using this correspondence, for example, the number of readout circuits can be reduced compared to Fig. 8(b), and therefore, for example, power consumption can be further reduced.

[0086] 8(a) and 8(b) can be similarly implemented for the drive circuit 150. In this case, power consumption can be further reduced.

[0087] (Other embodiments) The disclosed technology can also be realized by executing the following process. That is, the disclosed technology can also be realized by supplying software (programs) that realize one or more functions of the various embodiments described above to a system or device via a network or a storage medium, and having a computer (or a CPU, MPU, etc.) of the system or device read and execute the programs. The computer has one or more processors or circuits, and may include multiple separate computers or a network of multiple separate processors or circuits to read and execute computer-executable instructions. In this case, the processor or circuit may include a central processing unit (CPU), a microprocessing unit (MPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), or a field programmable gateway (FPGA). The processor or circuit may also include a digital signal processor (DSP), a data flow processor (DFP), or a neural processing unit (NPU).

[0088] The disclosure of this embodiment includes the following configuration, method, and program.

[0089] (Configuration 1) an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation; A plurality of readout means for reading out signals output from the plurality of pixel groups; a control means for controlling a first readout means for reading out a signal output from at least one pixel group including at least a part of the at least one candidate region to a first state and a second readout means for reading out a signal output from a pixel group not including the at least one candidate region to a second state consuming less power than the first state during a detection period in which the exposure dose is detected using the detection pixels when the pixel group does not include at least one candidate region selected as a region of interest from among a plurality of candidate regions included in an imaging region of the imaging means, A radiation imaging apparatus comprising:

[0090] (Configuration 2) the plurality of pixel groups further include imaging pixels for acquiring a radiographic image; 2. The radiation imaging apparatus according to configuration 1, wherein the control means controls the first readout means and the second readout means to be in the first state during an image acquisition period in which the radiation image is acquired using the imaging pixels.

[0091] (Configuration 3) The radiation imaging device of configuration 1 or 2, wherein the control means changes the second readout means from the second state to the first state and starts the image acquisition period after the exposure dose detected in the detection period reaches a threshold value.

[0092] (Configuration 4) The radiation imaging device of any one of configurations 1 to 3, wherein the control means controls the first readout means to the first state by supplying a first voltage to the first readout means during the detection period, and controls the second readout means to the second state by supplying a second voltage lower than the first voltage to the second readout means.

[0093] (Configuration 5) 5. The radiation imaging apparatus according to any one of configurations 1 to 4, wherein the region of interest is selected by an instruction from an operator.

[0094] (Configuration 6) 6. The radiation imaging apparatus according to any one of configurations 1 to 5, wherein the signals output from the plurality of pixel groups are read out by the plurality of readout devices, respectively.

[0095] (Configuration 7) the imaging means further includes a second pixel group not including the detection pixel, 7. The radiation imaging apparatus according to any one of configurations 1 to 6, wherein the control means controls a plurality of third readout means, which read out signals output from the plurality of second pixel groups, to the second state during the detection period.

[0096] (Configuration 8) 8. The radiation imaging apparatus according to configuration 7, wherein the plurality of candidate regions are included in any one of the plurality of pixel groups.

[0097] (Configuration 9) 8. The radiation imaging apparatus according to configuration 7, wherein the second pixel groups are read out by one of the third readout devices.

[0098] (Configuration 10) The radiation imaging device according to any one of configurations 1 to 9, wherein the control means controls the first readout means to the first state and the second readout means to the second state to obtain first correction data for correcting the exposure dose during a first period prior to the detection period, and corrects the exposure dose during the detection period using the first correction data.

[0099] (Configuration 11) The radiation imaging device according to any one of configurations 1 to 10, wherein the control means controls the first readout means to the first state and the second readout means to the second state to acquire second correction data for correcting the radiation image during a second period after the image acquisition period, and corrects the radiation image during the second period using the second correction data.

[0100] (Configuration 12) A radiation imaging device according to any one of configurations 1 to 11, further comprising a display control means for displaying a plurality of options and the plurality of candidate regions, and when one of the plurality of options is selected by instruction from an operator, controlling the display so as to highlight at least one candidate region selected as a region of interest from the plurality of candidate regions.

[0101] (Configuration 13) an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation; A plurality of readout means for reading out signals output from the plurality of pixel groups; a control means for controlling a first readout means for reading out signals output from a pixel group including at least one candidate region selected as a region of interest from among a plurality of candidate regions included in an imaging area of ​​the imaging means, to a first state, and for controlling a second readout means for reading out signals output from a pixel group not including the at least one candidate region, to a second state consuming less power than the first state; A radiation imaging apparatus comprising:

[0102] (Configuration 14) An information processing device that processes information; A radiation imaging apparatus according to any one of configurations 1 to 13, which is communicably connected to the information processing apparatus; A radiation imaging system comprising:

[0103] (Method 1) 1. A method for controlling a radiation imaging apparatus in which signals output from an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation are read out by a plurality of readout means, the method comprising the steps of: A control method for controlling, in the case where, among the multiple pixel groups, there is a pixel group that does not include at least one candidate region selected as a region of interest among a plurality of candidate regions included in an imaging area of ​​the imaging means, a first readout means that reads out a signal output from at least one pixel group that includes at least a portion of the at least one candidate region to a first state during a detection period in which the exposure dose is detected using the detection pixels, and a second readout means that reads out a signal output from a pixel group that does not include the at least one candidate region to a second state that consumes less power than the first state.

[0104] (Method 2) 1. A method for controlling a radiation imaging apparatus in which signals output from an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation are read out by a plurality of readout means, the method comprising the steps of: A control method for controlling a first readout means, which reads out signals output from a pixel group including at least one candidate region selected as a region of interest from among a plurality of candidate regions included in an imaging area of ​​the imaging means, to a first state in the plurality of pixel groups, and controlling a second readout means, which reads out signals output from a pixel group not including the at least one candidate region, to a second state consuming less power than the first state.

[0105] (Program 1) A program for causing a computer to execute the control method according to Method 1 or 2. [Explanation of symbols]

[0106] 100 Radiation imaging device 500 Radiography System 502 Information processing equipment 503 Access Point 505 Synchronous Control Device 506 Radiation Generator 508 Hospital LAN 510 Display section 511 Display control unit

Claims

1. an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation; A plurality of readout means for reading out signals output from the plurality of pixel groups; a control means for controlling a first readout means for reading out a signal output from at least one pixel group including at least a portion of the at least one candidate region, to a first state during a detection period in which the exposure dose is detected using the detection pixels, when the plurality of pixel groups includes a pixel group that does not include at least one candidate region selected as a region of interest from among a plurality of candidate regions included in an imaging area of ​​the imaging means, and for controlling a second readout means for reading out a signal output from a pixel group that does not include the at least one candidate region, to a second state consuming less power than the first state during a detection period in which the exposure dose is detected using the detection pixels; A radiation imaging apparatus comprising:

2. the plurality of pixel groups further include imaging pixels for acquiring a radiographic image; 2 . The radiation imaging apparatus according to claim 1 , wherein the control means controls the first readout means and the second readout means to be in the first state during an image acquisition period in which the radiation image is acquired using the imaging pixels.

3. 3. The radiation imaging device according to claim 2, wherein the control means changes the second readout means from the second state to the first state and starts the image acquisition period after the exposure dose detected during the detection period reaches a threshold value.

4. 2. The radiation imaging device according to claim 1, wherein the control means controls the first readout means to the first state by supplying a first voltage to the first readout means during the detection period, and controls the second readout means to the second state by supplying a second voltage lower than the first voltage to the second readout means.

5. 2. The radiation imaging apparatus according to claim 1, wherein the region of interest is selected by an instruction from an operator.

6. 2. The radiation imaging apparatus according to claim 1, wherein the signals output from the plurality of pixel groups are read out by the plurality of readout devices, respectively.

7. the imaging means further includes a second pixel group not including the detection pixel, 2. The radiation imaging apparatus according to claim 1, wherein the control means controls a plurality of third readout means for reading out signals output from the plurality of second pixel groups to the second state during the detection period.

8. The radiation imaging apparatus according to claim 7 , wherein the plurality of candidate regions are included in any one of the plurality of pixel groups.

9. 8. The radiation imaging apparatus according to claim 7, wherein the second pixel groups are read out by one of the third readout devices.

10. 2. The radiation imaging device according to claim 1, wherein the control means controls the first readout means to the first state and the second readout means to the second state to obtain first correction data for correcting the exposure dose during a first period prior to the detection period, and corrects the exposure dose during the detection period using the first correction data.

11. 2. The radiation imaging device according to claim 1, wherein the control means controls the first readout means to the first state and the second readout means to the second state to acquire second correction data for correcting the radiation image during a second period after the image acquisition period, and corrects the radiation image during the second period using the second correction data.

12. 2. The radiation imaging device according to claim 1, further comprising a display control means for displaying a plurality of options and the plurality of candidate regions, and when one of the plurality of options is selected by instruction from an operator, controlling the display so as to highlight at least one candidate region selected as a region of interest from among the plurality of candidate regions.

13. an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation; A plurality of readout means for reading out signals output from the plurality of pixel groups; a control means for controlling a first readout means for reading out signals output from a pixel group including at least one candidate region selected as a region of interest from among a plurality of candidate regions included in an imaging area of ​​the imaging means, to a first state, and for controlling a second readout means for reading out signals output from a pixel group not including the at least one candidate region, to a second state consuming less power than the first state; A radiation imaging apparatus comprising:

14. An information processing device that processes information; The radiation imaging apparatus according to claim 1 , which is communicably connected to the information processing apparatus; A radiation imaging system comprising:

15. A method for controlling a radiation imaging apparatus in which signals output from an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation are read out by a plurality of readout means, the method comprising the steps of: A control method for controlling a first readout means for reading out a signal output from at least one pixel group including at least a portion of the at least one candidate region, to a first state during a detection period in which the exposure dose is detected using the detection pixels, when the plurality of pixel groups includes a pixel group that does not include at least one candidate region selected as a region of interest among a plurality of candidate regions included in an imaging area of ​​the imaging means, and for controlling a second readout means for reading out a signal output from a pixel group that does not include the at least one candidate region, to a second state consuming less power than the first state.

16. A method for controlling a radiation imaging apparatus in which signals output from an imaging means having a plurality of pixel groups including detection pixels for detecting an exposure dose of radiation are read out by a plurality of readout means, the method comprising the steps of: A control method for controlling a first readout means, which reads out signals output from a pixel group including at least one candidate region selected as a region of interest from among a plurality of candidate regions included in an imaging area of ​​the imaging means, to a first state in the plurality of pixel groups, and controlling a second readout means, which reads out signals output from a pixel group not including the at least one candidate region, to a second state consuming less power than the first state.

17. A program for causing a computer to execute the control method according to claim 15 or 16.

Images