Radiation imaging device and radiation imaging system

Abstract

To provide a technique advantageous to improvement in detection precision of radiations.SOLUTION: A radiation imaging device includes: multiple pixels that are disposed in a matrix and includes at least a first pixel and a second pixel; a drive circuit for controlling the multiple pixels via multiple drive lines; and multiple signal lines to which signals are outputted from the multiple pixels. Each of the first pixel and the second pixel has an image element for acquiring a radiation image and a detection element for acquiring the dose of incident radiations. The detection element disposed in the first pixel and the detection element disposed in the second pixel are connected to the same signal line from among the multiple signal lines, and the drive circuit controls the detection element disposed in the first pixel and the detection element disposed in the second pixel such that the detection element disposed in the first pixel and the detection element disposed in the second pixel output signals to the same signal line at the same timing.SELECTED DRAWING: Figure 2

Description

Technical Field

[0001] The present invention relates to a radiation imaging apparatus and a radiation imaging system.

Background Art

[0002] In a radiation imaging apparatus, it is known to detect the dose of radiation incident on the radiation imaging apparatus and use it for imaging control. As such an imaging control technique, automatic exposure control (AEC) can be mentioned. Patent Document 1 shows a radiation image detection apparatus equipped with an AEC function.

Prior Art Documents

Patent Documents

[0003]

Patent Document 1

Summary of the Invention

Problems to be Solved by the Invention

[0004] Patent Document 1 shows that in addition to normal pixels for generating a radiation image, a composite pixel in which one pixel is divided into a main pixel for the radiation image and a sub-pixel for acquiring irradiation information is arranged. However, when one pixel is divided into a main pixel and a sub-pixel, the area of each pixel becomes smaller compared to the case where the pixel is not divided, so the sensitivity for detecting incident radiation decreases, and the accuracy for detecting irradiation information may decrease.

[0005] An object of the present invention is to provide a technique advantageous for improving the detection accuracy of radiation.

Means for Solving the Problems

[0006] In view of the above problems, a radiation imaging apparatus according to an embodiment of the present invention includes a plurality of pixels arranged in a matrix, the plurality of pixels including at least a first pixel and a second pixel, a drive circuit that controls the plurality of pixels via a plurality of drive lines, and a plurality of signal lines from which signals are output from the plurality of pixels. Each of the first pixel and the second pixel includes an image element for acquiring the radiation image and a detection element for acquiring the dose of incident radiation. The detection element arranged in the first pixel and the detection element arranged in the second pixel are connected to the same signal line among the plurality of signal lines, and the drive circuit controls the detection element arranged in the first pixel and the detection element arranged in the second pixel so that the detection element arranged in the first pixel and the detection element arranged in the second pixel output signals to the same signal line at the same timing.

Advantages of the Invention

[0007] According to the present invention, it is possible to provide a technique advantageous for improving the detection accuracy of radiation.

Brief Description of the Drawings

[0008]

Figure 1

Figure 2

Figure 3

Figure 4

Figure 5

Figure 6

Figure 7

Figure 8

Figure 9

Figure 10

Embodiments for Carrying Out the Invention

[0009] Hereinafter, embodiments will be described in detail with reference to the accompanying drawings. Note that the following embodiments do not limit the invention according to the claims. Although a plurality of features are described in the embodiments, not all of these plurality of features are essential to the invention, and the plurality of features may be arbitrarily combined. Further, in the accompanying drawings, the same or similar configurations are denoted by the same reference numerals, and redundant descriptions are omitted.

[0010] In addition, the radiation in the present disclosure is a beam formed by particles (including photons) emitted by radioactive decay, such as α-rays, β-rays, γ-rays, and also includes beams having energy equal to or higher than the same level, for example, X-rays, particle beams, cosmic rays, and the like.

[0011] With reference to FIGS. 1 to 10, a radiation imaging apparatus according to an embodiment of the present disclosure will be described. The following embodiments are all examples showing the present disclosure and do not limit the invention according to the claims. FIG. 1 is a diagram showing a configuration example of a radiation imaging system 500 including a radiation imaging apparatus 100. The radiation imaging system 500 includes a radiation imaging apparatus 100, a radiation source 501, a radiation source interface 502, a communication interface 503, and a controller 504. In the radiation imaging system 500, a subject 700 may be disposed between the radiation imaging apparatus 100 and the radiation source 501. FIG. 1 shows an example in which the radiation imaging apparatus 100 and the radiation source 501 perform wired communication, but a configuration for performing wireless communication may also be used.

[0012] The controller 504 can control each component of the radiation imaging system 500. Also, the controller 504 can function as a user interface for a user (such as a technician) to input various settings when using the radiation imaging system 500. For example, the dose, irradiation time (ms), tube current (mA), tube voltage (kV), the light collection field which is the area for detecting radiation, etc. are input to the controller 504. When the exposure switch attached to the radiation source 501 is operated, the controller 504 transmits a start request signal to the radiation imaging device 100. The start request signal is a signal requesting the start of radiation irradiation. In response to receiving the start request signal, the radiation imaging device 100 starts preparing to receive radiation irradiation. When the radiation imaging device 100 finishes preparing to capture a radiation image, it transmits a startable signal to the radiation source interface 502 via the communication interface 503. The startable signal is a signal notifying that the start of radiation irradiation is possible. In response to receiving the startable signal, the radiation source interface 502 causes the radiation source 501 to start radiation irradiation.

[0013] When the integrated value of the dose of the irradiated radiation reaches or is expected to reach the target threshold value, the radiation imaging device 100 transmits an end request signal to the radiation source interface 502 via the communication interface 503. The end request signal is a signal requesting the end of radiation irradiation. In response to receiving the end request signal, the radiation source interface 502 causes the radiation source 501 to end radiation irradiation at an appropriate timing. The target threshold value of the dose is determined based on the input value of the dose, the radiation irradiation intensity, the communication delay between each unit, the processing delay, etc.

[0014] The processing in the radiation source interface 502 according to the startable signal and end request signal output from the radiation imaging apparatus 100 may be performed by the controller 504. Also, for example, after imaging a radiation image, the controller 504 may process data for the radiation image output from the radiation imaging apparatus and display the radiation image on a display (not shown) or the like. It can also be said that the radiation source interface 502 and the controller 504 function as a signal processing unit that processes signals output from the radiation imaging apparatus 100.

[0015] FIG. 2 is a diagram showing a configuration example of the radiation imaging apparatus 100 of the present disclosure. The radiation imaging apparatus 100 includes a plurality of pixels 101, 104, a drive circuit 150, and a plurality of signal lines 120. The plurality of pixels 101, 104 are arranged in a matrix in the imaging region IR so as to form a plurality of rows and a plurality of columns in order to acquire a radiation image. The drive circuit 150 drives the plurality of pixels 101, 104 via a plurality of drive lines 110, 111. Signals are output from the plurality of pixels 101, 104 to the plurality of signal lines 120. Among the drive lines 110, 111, the drive line 110 is arranged corresponding to each row of the pixels 101 arranged over a plurality of rows in the imaging region IR, and each drive line 110 corresponds to any one pixel row. The plurality of signal lines 120 are arranged corresponding to each column of the pixels 101 arranged over a plurality of columns in the imaging region IR, and each signal line 120 corresponds to any one pixel column.

[0016] Among the plurality of pixels 101, 104, the pixel 101 is a pixel used to acquire a radiation image. Among the plurality of pixels 101, 104, the pixel 104 is a pixel used to acquire (monitor) the dose of radiation incident separately from the radiation image. In the present embodiment, two or more pixels 104 are arranged in the imaging region IR.

[0017] Pixel 101 includes a conversion element 102 for converting incident radiation into an electrical signal, and a switch element 103 that connects the signal line 120 corresponding to each pixel column and the conversion element 102 to each other. The conversion element 102 arranged in pixel 101 is an image element for acquiring a radiation image. Pixel 104 includes a conversion element 105 for converting incident radiation into an electrical signal, and a switch element 106 that connects a predetermined signal line 120 and the conversion element 105 to each other. The conversion element 105 arranged in pixel 104 is a detection element for acquiring the dose of radiation incident separately from the radiation image. Pixel 104 is arranged so as to be included in the rows and columns constituted by a plurality of pixels 101.

[0018] The conversion elements 102 and 105 may be constituted by a scintillator that converts radiation into light, and a photoelectric conversion element that converts the light emitted from the scintillator into an electrical signal. In that case, the scintillator is generally formed in a sheet shape so as to cover the imaging region IR and can be shared by a plurality of pixels 101 and 104. Alternatively, the conversion elements 102 and 105 may be constituted by conversion elements that directly convert radiation into an electrical signal.

[0019] The switch elements 103 and 106 may include, for example, thin film transistors (TFTs) in which an active region is constituted by a semiconductor such as amorphous silicon or polycrystalline silicon. However, it is not limited thereto, and any appropriate element may be used as long as the switch elements 103 and 106 can control the connection or non-connection between the conversion elements 102 and 105 and the signal line 120.

[0020] The conversion elements 102 and 105 include a first electrode and a second electrode. The switch elements 103 and 106 include a first main electrode, a second main electrode, and a control electrode. The first electrode of the conversion element 102 is connected to the first main electrode of the switch element 103, and the second electrode of the conversion element 102 is connected to the bias line 130. The bias line 130 extends in the column direction in the imaging region IR and is commonly connected to the second electrodes of a plurality of conversion elements 102 arranged in the column direction. The bias line 130 receives the supply of the bias voltage Vs from the power supply circuit 140. The second main electrode of the switch element 103 arranged in one or more pixels 101 arranged in one pixel column is connected to one signal line 120. The control electrode of the switch element 103 arranged in one or more pixels 101 arranged in one row is connected to one drive line 110. The control electrode of the switch element 106 arranged in the pixel 104 is connected to a drive line 111 different from the drive line 110 to which the switch element 103 arranged in the pixel 101 is connected.

[0021] The drive circuit 150 is configured to supply drive signals to the pixels 101 and 104 connected to the respective drive lines 110 and 111 via the plurality of drive lines 110 and 111 according to the control signals supplied from the control circuit 180. The drive line 110 and the drive line 111 may be connected to different drive circuits respectively. Specifically, the drive line 110 may be connected to an imaging drive circuit for acquiring a radiation image, and the drive line 111 may be connected to a drive circuit for detecting the dose of radiation incident separately from the radiation image.

[0022] In this embodiment, the drive signal supplied by the drive circuit 150 is a signal for turning on (conducting) the switch elements 103 and 106 included in the pixels 101 and 104 to be driven. Hereinafter, the switch elements 103 and 106 arranged in the respective pixels 101 and 104 will be described as turning on when the signal supplied from the drive circuit 150 is at a high level and turning off when it is at a low level. Therefore, the high-level signal supplied from the drive circuit 150 is referred to as the drive signal. When the drive signal is supplied to the pixels 101 and 104, the signals accumulated in the conversion elements 102 and 105 arranged in the pixels 101 and 104 to which the drive signal is supplied become readable by the readout circuit 160.

[0023] The readout circuit 160 is configured to read signals from a plurality of pixels 101 and 104 via a plurality of signal lines 120. The readout circuit 160 may include a plurality of amplifier circuits 161, a multiplexer 162, and an analog-to-digital (AD) converter 163. Each of the plurality of signal lines 120 is connected to a corresponding amplifier circuit 161 among the plurality of amplifier circuits 161 arranged in the readout circuit 160. One signal line 120 corresponds to one amplifier circuit 161. The multiplexer 162 selects the plurality of amplifier circuits 161 in a predetermined order and supplies the signal supplied from the selected amplifier circuit 161 to the AD converter 163. The AD converter 163 converts the supplied signal into a digital signal and outputs it.

[0024] The signal read out from pixel 101 is supplied to processing circuit 170, and processing such as calculation and storage is performed by processing circuit 170. It can also be said that processing circuit 170 processes the signals output to a plurality of signal lines 120. Specifically, processing circuit 170 may include arithmetic circuit 171 and memory 172. Arithmetic circuit 171 generates data for displaying a radiation image based on the signal read out from pixel 101 and supplies it to control circuit 180. The signal read out from pixel 104 is supplied to processing circuit 170, and processing such as calculation is performed by arithmetic circuit 171 arranged in processing circuit 170, and the calculation result may be stored in memory 172. Specifically, processing circuit 170 supplies information indicating irradiation of radiation to radiation imaging apparatus 100 to control circuit 180 based on the signal read out from pixel 104. For example, processing circuit 170 may detect irradiation of radiation to radiation imaging apparatus 100, may detect the dose of incident radiation, or may acquire (determine) the integrated dose of incident radiation.

[0025] Control circuit 180 controls each component of radiation imaging apparatus 100. For example, control circuit 180 may control drive circuit 150 and readout circuit 160 based on the information from processing circuit 170. Also, for example, control circuit 180 may control the start and end of exposure (accumulation of charge corresponding to radiation irradiated by pixel 101) in radiation imaging apparatus 100 based on the information from processing circuit 170.

[0026] To determine the dose of radiation incident on the radiation imaging apparatus 100 during radiation irradiation, the control circuit 180 controls the drive circuit 150 to, for example, scan only the drive line 111 and make it possible to read out signals only from the pixel 104. Next, the control circuit 180 controls the readout circuit 160 to read out the signals of the pixel column in which the pixel 104 is arranged via the corresponding signal line 120 and supply them to the processing circuit 170. The processing circuit 170 supplies information indicating the radiation irradiation on the radiation imaging apparatus 100, such as the dose of the incident radiation, to the control circuit 180 based on the signals read out from the pixel 104. By such an operation, the radiation imaging apparatus 100 can obtain irradiation information on the pixel 104 during radiation irradiation.

[0027] In the present embodiment, as shown in FIG. 2, two pixels 104a and 104b each including a detection element (conversion element 105) for detecting the dose of radiation incident separately from the radiation image are arranged adjacent to each other. It can also be said that the pixel 104a and the pixel 104b are arranged adjacent to each other in the direction (row direction) in which a plurality of drive lines 110 and 111 extend. In that case, the conversion element 105 arranged in the pixel 104a and the conversion element 105 arranged in the pixel 104b are connected to the same signal line 120a among the plurality of signal lines 120. Further, the pixels 104a and 104b are connected to the same drive line 111a among the plurality of drive lines 110 and 111. The pixels 104a and 104b are connected in this way. Thereby, during radiation irradiation, the drive circuit 150 can control the conversion element 105 arranged in the pixel 104a and the conversion element 105 arranged in the pixel 104b to output signals to the same signal line 120a at the same timing. That is, during radiation irradiation, the signal amount per one signal line 120 for obtaining irradiation information such as the incident dose can be increased by two pixels. Thereby, the accuracy of detecting the dose of the incident radiation can be improved.

[0028] For example, when two adjacent pixels 104 are connected to signal lines 120 corresponding to different pixel columns, after reading out signals including noise superimposed on each signal line 120, the signals of the two pixels 104 are, for example, added together by the processing circuit 170. Therefore, compared with the present embodiment in which signals are output from two pixels 104 to one signal line 120a, when two pixels 104 are connected to separate signal lines, the amount of noise with respect to the signal corresponding to the incidence of radiation increases. By connecting two adjacent pixels 104 to one signal line 120a as in the present embodiment, for the signal corresponding to the incidence of radiation for two pixels, the noise is only the amount superimposed on one signal line 120a. Thereby, the accuracy of detecting the dose of incident radiation can be improved.

[0029] As shown in FIG. 2, pixels 104c and 104d arranged in different rows may be connected to the same signal line 120a to which pixels 104a and 104b are connected. Pixels 104c and 104d are arranged adjacent to each other. It can also be said that pixels 104c and 104d are arranged adjacent to each other in the direction (row direction) in which a plurality of drive lines 110 and 111 extend. Pixels 104c and 104d are connected to the same drive line 111 among the plurality of drive lines 110 and 111. In the direction (column direction) intersecting the direction in which drive lines 110 and 111 extend, pixels 101 provided with conversion elements 102 for acquiring a radiation image among the plurality of pixels 101 and 104 may be arranged between the combination of pixels 104a and 104b and the combination of pixels 104c and 104d. Although the operation example will be described later, during irradiation with radiation, the drive circuit 150 may control so that the conversion elements 105 arranged in pixel 104c and the conversion elements 105 arranged in pixel 104d output signals to the same signal line 120a at the same timing. Further, in that case, during irradiation with radiation, the drive circuit 150 may control so that the conversion elements 105 arranged in pixels 104a, 104b, 104c, and 104d output signals to the same signal line 120a at the same timing.

[0030] Also, for example, a combination of pixels 104 arranged in the same row as pixels 104a and 104b (which are commonly connected to a signal line 120 different from pixels 104a and 104b) may be arranged adjacent to the combination of pixels 104a and 104b. Also, for example, a combination of pixels 104 arranged in the same row as pixels 104a and 104b (which are commonly connected to a signal line 120 different from pixels 104a and 104b) may have one or more pixels 101 sandwiched therebetween and the combination of pixels 104a and 104b.

[0031] FIG. 3 shows a detailed circuit configuration example of the amplifier circuit 161. The amplifier circuit 161 may include a differential amplifier circuit AMP and a sample hold circuit SH. The differential amplifier circuit AMP amplifies and outputs the signal appearing on the signal line 120. The control circuit 180 can reset the potential of the signal line 120 by supplying a control signal φR to the switch element of the differential amplifier circuit AMP. The output of the differential amplifier circuit AMP can be held by the sample hold circuit SH. The control circuit 180 causes the sample hold circuit SH to hold a signal by supplying a control signal φSH to the switch element of the sample hold circuit SH. The signal held in the sample hold circuit SH is read out by the multiplexer 162.

[0032] Next, with reference to FIG. 4, an operation example of the radiation imaging apparatus 100 having the configuration shown in FIG. 2 will be described. In each of the following figures including FIG. 4 for describing the operation example, Vg (Vg1 to Vgn) indicates the drive signal supplied to each drive line 110, and the timing at which the drive signal is supplied is shown at a high level. Similarly, Vd (Vd1, Vd2) indicates the drive signal supplied to each drive line 111, and the timing at which the drive signal is supplied is shown at a high level.

[0033] The radiation imaging apparatus 100 starts a reset operation at time t0 and repeats the reset operation. The reset operation is an operation of sequentially supplying drive signals to the drive lines 110 and 111 to reset the dark charges and the like accumulated in the conversion elements 102 and 105 arranged in the pixels 101 and 104.

[0034] At time t1, the radiation imaging apparatus performs the same readout operation as the readout operation performed during the radiation irradiation, and performs an offset signal readout operation to obtain a correction value Od of the offset signal of pixel 104. The readout operation performed during the radiation irradiation is an operation of supplying a drive signal to drive line 111 and reading out the signal accumulated in conversion element 105 arranged in pixel 104. By obtaining the correction value Od of the offset signal before receiving the radiation irradiation start request signal, the correction value Od can be obtained without affecting the radiation exposure delay. Therefore, it becomes possible to perform the readout operation as the offset signal readout operation many times (for example, several thousand times), and for example, the read out signals can be averaged. Thereby, the influence of noise when reading out the signal with respect to the correction value Od of the offset signal can be reduced, and the correction accuracy can be improved.

[0035] After performing the offset signal readout operation a predetermined number of times, the reset operation is repeated again from time t2. When a radiation irradiation start request signal is received at time t3, after performing the reset operation up to the last row of the pixel rows arranged in the imaging region IR, the readout operation performed during the radiation irradiation is started from time t4. Next, an enable signal is transmitted at time t5, and radiation irradiation is started from radiation source 501 at time t6.

[0036] Since the correction value Od of the offset signal has been obtained, it is possible to start the radiation irradiation immediately after receiving the start request signal, and the exposure delay corresponding to the time for obtaining the correction value Od of the offset signal can be shortened. Also, after shifting from the reset operation to the readout operation at time t4, the enable signal may be transmitted and the radiation irradiation may be started after a predetermined time (for example, several ms to several tens of ms) has elapsed. Thereby, it is possible to suppress reading out a signal corresponding to the incident radiation during a period in which the output fluctuation is large immediately after the operation switching from the reset operation to the readout operation. After the radiation irradiation is started, correction is performed on the signal value Sd of the signal read out from pixel 104 using the correction value Od of the offset signal, and the dose of the incident radiation can be determined.

[0037] That is, before the radiation irradiation, the processing circuit 170 acquires a signal value (correction value Od) based on the signals output by the driving circuit 150 to the conversion elements 105 respectively arranged in the pixels 104a and 104b on the same signal line 120a at the same timing. Next, during the radiation irradiation, the processing circuit 170 corrects the signal value Sd corresponding to the signals output by the conversion elements 105 respectively arranged in the pixels 104a and 104b to the same signal line 120a at the same timing, using the correction value Od, and based on the corrected signal value Sd, acquires the dose DOSE of the incident radiation. Specifically, for the signal value Sd read out during the radiation irradiation, DOSE = Sd - Od as shown, the difference is calculated for correction.

[0038] In the example shown in FIG. 4, before the radiation irradiation, the driving circuit 150 performs a reset operation to reset each of the plurality of pixels 101 and 104, and at least one (for example, several thousand times) offset signal readout operation to output signals to the conversion elements 105 respectively arranged in the pixels 104 at the same timing. At that time, the processing circuit 170 acquires the correction value Od based on the signals obtained in the offset signal readout operation. In the operation shown in FIG. 4, before the radiation start request signal by the user is input, the driving circuit 150 starts the offset signal readout operation. Thereby, as described above, the exposure delay can be shortened. However, it is not limited thereto, and in response to the input of the radiation irradiation start request by the user, the driving circuit 150 may end the reset operation and start the offset signal readout operation. In that case, in response to the end of the offset signal readout operation, the radiation imaging apparatus 100 may transmit it to the radiation source interface 502 via the communication interface 503. By acquiring the correction value Od of the offset signal immediately before the radiation irradiation in this way, the influence of the offset variation caused by the temperature change or the like of the radiation imaging apparatus 100 can be suppressed.

[0039] The processing circuit 170 may correct the signal value of the signal output from the pixel 104 during the irradiation of radiation according to the sensitivity of the pixel 101 for acquiring a radiation image. In the automatic exposure control (AEC) performed by acquiring the dose of radiation incident during the irradiation of radiation, the dose of irradiation rays to the pixel 101 arranged around the pixel 104 is detected (determined) by monitoring the signal amount of the pixel 104. Therefore, by correcting the signal value of the signal output from the pixel 104, the sensitivity of the pixel 104 to radiation is made close to (matched with) the sensitivity of the pixel 101 to radiation. Thereby, the detection accuracy of the dose of radiation irradiated to the pixel 101 can be improved.

[0040] Also, by adding up the signal values of the signals output from a plurality of pixels 104 arranged in the imaging region IR, the signal amount can be increased to reduce the influence of noise and improve the dose detection accuracy. Therefore, the processing circuit 170 may acquire (determine) the dose of incident radiation based on the sum of the signal values of the signals output from a plurality of conversion elements 105 including the conversion elements 105 respectively arranged in the pixel 104a and the pixel 104b. At this time, as shown in FIG. 4, drive signals may be supplied to the plurality of drive lines 111 at the same timing (Vd1 and Vd2 are at the high level simultaneously). Thereby, signals are simultaneously supplied to the signal line 120a from combinations of the pixels 104a and 104b arranged in different rows and combinations of the pixels 104c and 104d. The threshold value for determining the irradiation amount of radiation (for example, outputting an end request signal) may be set according to the sum value of the signal values of the signals output from the plurality of pixels 104 arranged in the imaging region IR.

[0041] FIG. 5 is a diagram showing a modified example of the radiation imaging apparatus 100 shown in FIG. 2. The difference from the configuration shown in FIG. 2 is that a pixel 107 is arranged instead of the pixel 104. Since the other configurations may be the same as the configuration shown in FIG. 2, here, the description will focus on the different configurations.

[0042] Pixel 107, like pixel 104, is a pixel that has a function of acquiring (monitoring) the dose of radiation incident separately from the radiation image. Further, pixel 107, like pixel 101, is a pixel that has a function of acquiring a radiation image. Specifically, pixel 107 includes a conversion element 108a, which is an image element for acquiring a radiation image, and a conversion element 108b, which is a detection element for acquiring the dose of radiation incident separately from the radiation image. Also, pixel 107 includes a switch element 109a that connects the conversion element 108a and a signal line 120 corresponding to each pixel column in which pixel 107 is arranged to each other, and a switch element 109b that connects the conversion element 108b and a predetermined signal line 120 to each other.

[0043] Similar to pixel 104 in the configuration shown in FIG. 2, in the radiation imaging apparatus 100 shown in FIG. 5, two or more pixels 107 are arranged in the imaging region IR. Here, two pixels 107a and 107b among the pixels 107 will be described in detail.

[0044] Similar to the relationship between pixel 104a and pixel 104b described above, the conversion element 108b arranged in pixel 107a and the conversion element 108b arranged in pixel 107b are connected to the same signal line 120a among the plurality of signal lines 120. In that case, during the irradiation of radiation, the drive circuit 150 controls the conversion element 108b arranged in pixel 107a and the conversion element 108b arranged in pixel 107b to output signals to the same signal line 120a at the same timing.

[0045] If the conversion elements 108b arranged in each of the pixel 107a and the pixel 107b are connected to the same signal line 120a and are controlled to output signals at the same timing, they may be arranged in any positional relationship within the imaging region IR. For example, the pixel 107a and the pixel 107b may be arranged in different pixel rows. In that case, the pixel 107a and the pixel 107b may be arranged in the same pixel column, or may be arranged in different pixel columns. Here, the pixel region in which the pixels 101 and 107 are arranged may be a rectangular region delimited by the signal lines 120 and the drive lines 110. One pixel 101 or one pixel 107 is arranged in each pixel region. A pixel row is constituted by pixel regions arranged in the row direction, and a pixel column is constituted by pixel regions arranged in the column direction.

[0046] Also, as shown in FIG. 5, the pixel 107a and the pixel 107b may be arranged adjacent to each other. For example, the pixel 107a and the pixel 107b may be arranged adjacent to each other in the direction (row direction) in which the plurality of drive lines 110 and 111 extend.

[0047] Also, the conversion elements 108b arranged in the pixel 107a and the pixel 107b may be connected to the same drive line 111 among the plurality of drive lines 111. In that case, the conversion elements 108b for detecting the dose of incident radiation arranged in the pixel 107a and the pixel 107b respectively are connected to a drive line 111 different from the drive line 110 to which the conversion element 108a for acquiring a radiation image arranged in the pixel 107a and the pixel 107b respectively is connected.

[0048] The operation of reading out signals from the conversion element 108b arranged in the pixels 107a and 107b is the same as the operation of reading out signals from the conversion element 105 arranged in the pixels 104a and 104b described with reference to FIG. 4 above. Therefore, the description of the operation of the radiation imaging apparatus 100 shown in FIG. 5 is omitted. However, since the conversion element 108a for acquiring a radiation image is arranged in the pixel 107, in the reset operation, the conversion element 108a is also reset, and when signals for acquiring a radiation image are read out, signals are read out from the conversion element 102 arranged in the pixel 101 and the conversion element 108a arranged in the pixel 107, respectively.

[0049] As shown in FIG. 5, a conversion element 108a for acquiring a radiation image and a conversion element 108b for detecting the dose of incident radiation are arranged in one pixel 107. Thereby, in the pixel 107, while holding a signal for acquiring a radiation image in the conversion element 108a, the dose of incident radiation can be detected using the conversion element 108b. Also, by dividing the conversion element arranged in one pixel 107 into conversion elements 108a and 108b, the areas of the conversion elements 108a and 108b become smaller, and the sensitivity for detecting incident radiation decreases for each. However, as in the present disclosure, during irradiation with radiation, signals are output from the conversion elements 108b arranged in two or more pixels 107 to the same signal line 120 at the same timing. Thereby, during irradiation with radiation, the signal amount per one signal line 120 for obtaining irradiation information of radiation such as the incident dose can be increased by two or more conversion elements. Thereby, the accuracy of detecting the dose of incident radiation can be improved.

[0050] As shown in FIG. 5, pixels 107c and 107d arranged in different rows may be connected to the same signal line 120a to which pixels 107a and 107b are connected. Pixels 107c and 107d may be arranged apart from each other with a pixel 101 arranged therebetween, or may be arranged adjacent to each other as shown in FIG. 5. As shown in FIG. 5, pixels 107c and 107d may be arranged adjacent to each other in the direction (row direction) in which a plurality of drive lines 110 and 111 extend. Pixels 107c and 107d are connected to the same drive line 111 among the plurality of drive lines 110 and 111. In the direction (column direction) intersecting with the direction in which the drive lines 110 and 111 extend, a pixel 101 including a conversion element 102 for acquiring a radiation image may be arranged between a combination of pixels 107a and 107b and a combination of pixels 107c and 107d among the plurality of pixels 101 and 107. During radiation irradiation, the drive circuit 150 may control such that the conversion element 108b arranged in pixel 107c and the conversion element 108b arranged in pixel 107d output signals to the same signal line 120a at the same timing. Further, in that case, during radiation irradiation, the drive circuit 150 may control such that the conversion elements 108b respectively arranged in pixels 107a, 107b, 107c, and 107d output signals to the same signal line 120a at the same timing.

[0051] Also, for example, a combination of pixels 107 arranged in the same row as pixels 107a and 107b (which are commonly connected to a signal line 120 different from that of pixels 107a and 107b) may be arranged adjacent to the combination of pixels 107a and 107b. Also, for example, a combination of pixels 107 arranged in the same row as pixels 107a and 107b (which are commonly connected to a signal line 120 different from that of pixels 107a and 107b) may be arranged with one or more pixels 101 sandwiched therebetween and the combination of pixels 107a and 107b.

[0052] Similarly to the above, in the automatic exposure control (AEC), the radiation dose to the pixels 101 arranged around the pixel 107 is detected (determined) by monitoring the signal value of the signal output from the conversion element 108b arranged in the pixel 107. Therefore, the processing circuit 170 may correct the signal value of the signal output from the conversion element 108b arranged in the pixel 107 during the radiation irradiation according to the difference in sensitivity to radiation between the conversion element 108b arranged in the pixel 107 and the conversion element 102 arranged in the pixel 101. By correcting the signal value of the signal output from the conversion element 108b arranged in the pixel 107, the detection accuracy of the dose irradiated to the pixel 101 can be improved. Further, when generating a radiation image, the signal value of the signal output from the conversion element 108a arranged in the pixel 107 may be corrected according to the difference in sensitivity to radiation between the conversion element 108a arranged in the pixel 107 and the conversion element 102 arranged in the pixel 101.

[0053] FIG. 6 is a diagram showing a modified example of the radiation imaging apparatus 100 shown in FIG. 2. The difference from the configuration shown in FIG. 2 is that a pixel 114 is arranged in addition to the pixels 101 and 104. Since the other configurations may be the same as those shown in FIG. 2, the different configurations will be mainly described here.

[0054] Pixel 114 has the same structure as pixel 104. Pixel 114 can be arranged to detect the dose of radiation incident separately from the radiation image, similar to pixel 104. In the imaging region IR, two or more pixels 114 are arranged in the same way as pixel 104. Each of the pixels 114 includes a conversion element 115 that has a different sensitivity to radiation from the conversion element 105 arranged in pixel 104. For example, the conversion element 115 has a shielding portion arranged on the side where the radiation enters, and is a conversion element that does not have sensitivity to radiation. When the conversion element 115 is composed of a scintillator that converts radiation into light and a photoelectric conversion element that converts the light emitted from the scintillator into an electrical signal, for example, a light-shielding layer is arranged as a shielding portion between the scintillator and the photoelectric conversion element. The light-shielding layer may be composed of a metal such as aluminum and may function as a wiring pattern within the imaging region IR. Also, when the conversion element 115 is a conversion element that directly converts radiation into an electrical signal, for example, a metal layer such as lead or tungsten is arranged as a shielding portion on the side where the radiation of the conversion element 115 enters.

[0055] Since pixel 114 has the same structure as pixel 104 but a different sensitivity to radiation from pixel 104 (for example, no sensitivity), by reading out the signal accumulated in pixel 114, the signal corresponding to the dark component of pixel 104 can be monitored. For example, as shown in FIG. 6, pixels 114a and 114b are arranged. Also, the conversion element 115 which is a detection element arranged in pixel 114a and the conversion element 115 which is a detection element arranged in pixel 114b are connected to a signal line 120b different from the signal line 120 among the plurality of signal lines 120. Pixel 104a, 104b and pixels 114a, 114b may be arranged in the same pixel row as shown in FIG. 6, or may be arranged in different pixel rows. As shown in FIG. 6, when pixel 104a, 104b and pixels 114a, 114b are arranged in the same pixel row, the conversion element 105 arranged in pixel 104a, 104b respectively and the conversion element 115 arranged in pixel 114a, 114b respectively may be connected to the same drive line 111 among the plurality of drive lines 111.

[0056] FIG. 7 is a diagram showing an operation example of the radiation imaging apparatus 100 having the configuration shown in FIG. 6. It is the same operation as the operation shown in FIG. 4, except that signals are read from the pixels 104 and 114 during the offset signal read operation and during the read operation during radiation irradiation. In the offset signal read operation before radiation irradiation, the same read operation as during radiation irradiation is performed. Similar to the operation shown in FIG. 4, the processing circuit 170 acquires the correction value Od of the offset signal of the pixel 104. Further, in the offset signal read operation before radiation irradiation, the processing circuit 170 acquires the correction value Oc of the offset signal of the pixel 114 from the signal value based on the signals output to the signal line 120b at the same timing by the conversion elements 115 respectively arranged in the pixels 114a and 114b by the drive circuit 150.

[0057] Next, during radiation irradiation, similar to the operation shown in FIG. 4, the processing circuit 170 acquires the signal value Sd corresponding to the signals output to the same signal line 120a at the same timing by the conversion elements 105 respectively arranged in the pixels 104a and 104b. Further, the processing circuit 170 acquires the signal value Sc corresponding to the signals output to the signal line 120b at the same timing by the conversion elements 115 respectively arranged in the pixels 114a and 114b by the drive circuit 150. The processing circuit 170 corrects the signal value Sd using the correction value Od, and similarly corrects the signal value Sc using the correction value Oc, and acquires the dose DOSE of the incident radiation based on the corrected signal value Sd and the signal value Sc. Specifically, for the signal values Sd and Sc read during radiation irradiation, DOSE = (Sd - Od) - (Sc - Oc) As shown, the difference is calculated for correction.

[0058] In the configuration shown in FIGS. 6 and 7, signals can be read out at the same timing from the conversion elements 105 respectively arranged in the pixels 104a and 104b and the conversion elements 115 respectively arranged in the pixels 114a and 114b. By correcting the signal value of the signal of the pixel 104 using the signal value of the signal of the pixel 114 read out at the same timing, the dark component included in the signal output from the pixel 104 can be corrected more appropriately. Further, by using the correction values Od and Oc of the offset signals of the respective pixels 104 and 114, the differences in the inherent characteristics of the respective pixels 104 and 114 (for example, differences in the channels of the detection circuits, parasitic resistances added to the pixels, differences in parasitic capacitances, etc.) can be corrected.

[0059] FIG. 8 is a diagram showing an operation example different from the operation example shown in FIG. 7 of the radiation imaging apparatus 100 having the configuration shown in FIG. 6. The difference from the operation example of FIG. 7 is that sampling and holding are performed without supplying a drive signal to the drive line 111 during the offset signal readout operation and during the readout operation during radiation irradiation, and sampling and holding are performed after supplying the drive signal, alternately. Other than that, the operation may be the same as that of FIG. 7.

[0060] In a readout operation where sample holding is performed after supplying a drive signal, the above-described signal values Sd, Sc, and correction values Od, Oc are obtained. Therefore, a readout operation in which sample holding is performed without supplying a drive signal to the drive line 111 during the offset signal readout operation and during the readout operation under radiation irradiation will be described. Sample holding is performed without supplying a drive signal to the drive line 111. As a result, before radiation irradiation, the processing circuit 170 obtains a correction value Od' of the offset signal from the signal value of the signal line 120 at a timing when the drive circuit 150 does not output a signal to the conversion elements 105 respectively arranged in the pixels 104a, 104b on the same signal line 120a. Similarly, the processing circuit 170 obtains a correction value Oc' of the offset signal from the signal value of the signal line 120b at a timing when the drive circuit 150 does not output a signal to the conversion elements 115 respectively arranged in the pixels 114a, 114b on the signal line 120b. Next, during radiation irradiation, the processing circuit 170 obtains a signal value Sd' of the signal line 120 at a timing when the drive circuit 150 does not output a signal to the conversion elements 105 respectively arranged in the pixels 104a, 104b on the same signal line 120a. Similarly, the processing circuit 170 obtains a signal value Sc' of the signal line 120b at a timing when the drive circuit 150 does not output a signal to the conversion elements 115 respectively arranged in the pixels 114a, 114b on the signal line 120b.

[0061] The processing circuit 170 corrects the signal value Sd using the correction value Od, corrects the signal value Sc using the correction value Oc, corrects the signal value Sd' using the correction value Od', corrects the signal value Sc' using the correction value Oc', and obtains the dose DOSE of the incident radiation based on the corrected signal values Sd, signal value Sc, signal value Sd' and signal Sc'. Specifically, DOSE = {(Sd - Od) - (Sd' - Od')} - {(Sc - Oc) - (Sc' - Oc')} As shown, differences are calculated for correction.

[0062] The effects of this correction will be described below. A parasitic capacitance is formed between one signal line 120 and the electrode of the conversion element included in the pixel connected to the signal line 120. Due to this parasitic capacitance, the signal line 120 and the electrode of the conversion element are capacitively coupled, and crosstalk may occur. Therefore, while a signal is being read out from the conversion element of the pixels in a certain row via the signal line 120, if the potential of the electrode of the conversion element of the pixels in another row changes due to photoelectric conversion, the potential of the signal line 120 may change due to crosstalk. This change can be a factor that deteriorates the accuracy in detecting (determining) the dose of the incident radiation. In the above-described operation, in order to acquire a signal based on the potential of the signal line 120 without turning on the switch element 106 without supplying a drive signal, a signal caused by crosstalk can be extracted. Then, after supplying a drive signal to turn on the switch element 106, a signal is read out. Thereby, a signal obtained by adding up the signals accumulated in the conversion elements 105 and 115 in addition to crosstalk can be read out. If the time from resetting the potential of the signal line 120 to sampling to obtain a signal from the signal line 120 is substantially the same regardless of the presence or absence of the drive signal, the amount of crosstalk will be substantially the same. Therefore, by taking the difference between them, crosstalk can be corrected. Furthermore, the fact that the offset component and the dark component can be corrected is the same as the correction of the operation shown in FIG. 7.

[0063] FIG. 9 is a diagram showing a modified example of the radiation imaging apparatus 100 shown in FIG. 5. The difference from the configuration shown in FIG. 5 is that, similar to the difference between the configuration shown in FIG. 2 and the configuration shown in FIG. 6, a pixel 117 is arranged in addition to the pixels 101 and 107.

[0064] Pixel 117 has the same structure as pixel 107. Pixel 117 can be arranged to detect the dose of radiation incident separately from the radiation image, similar to pixel 107. In the imaging region IR, two or more pixels 117 are arranged in the same way as pixel 107. Each of the pixels 117 includes a conversion element 118b that has a different sensitivity to radiation from the conversion element 108b arranged in pixel 107. For example, a shielding portion is arranged on the side of the conversion element 118b where radiation enters, and the conversion element 118b is a conversion element that has no sensitivity to radiation. When the conversion element 118b is composed of a scintillator that converts radiation into light and a photoelectric conversion element that converts the light emitted from the scintillator into an electrical signal, for example, a light-shielding layer is arranged as a shielding portion between the scintillator and the photoelectric conversion element. The light-shielding layer may be composed of a metal such as aluminum and may function as a wiring pattern within the imaging region IR. Also, when the conversion element 118b is a conversion element that directly converts radiation into an electrical signal, for example, a metal layer such as lead or tungsten is arranged on the side of the conversion element 118b where radiation enters as a shielding portion.

[0065] The relationship between the pixel 104 shown in FIG. 2 and the pixel 107 shown in FIG. 5 described above can be applied to the relationship between the pixels 104, 114 shown in FIG. 6 and the pixels 104, 114 shown in FIG. 9. Also, for example, the operation of reading signals from the conversion element 108b arranged in pixel 107 and the conversion element 118b arranged in pixel 117 is the same as the operation of reading signals from the conversion element 105 arranged in pixel 104 and the conversion element 115 arranged in pixel 114 described with reference to FIGS. 7 and 8 above. Therefore, the description of the operation of the radiation imaging apparatus 100 shown in FIG. 9 is omitted. However, since a conversion element 118a for acquiring a radiation image is arranged in pixel 117, in the reset operation, the conversion element 118a is also reset, and when a signal for acquiring a radiation image is read out, signals are read out from the conversion element 102 arranged in pixel 101 and the conversion element 118a arranged in pixel 117, respectively.

[0066] In the configuration shown in FIG. 9, pixel 117a and pixel 117b are arranged adjacent to each other. However, it is not limited thereto. If the conversion elements 118b arranged in pixel 117a and pixel 117b are connected to the same signal line 120 and can output signals at the same timing, pixel 117a and pixel 117b may be arranged apart from each other.

[0067] As shown in FIG. 9, a conversion element 108a for acquiring a radiation image and conversion elements 108b, 118b for detecting the dose of incident radiation are arranged in one pixel 107, 117. Thereby, in pixel 107, while holding a signal for acquiring a radiation image in conversion element 108a, the dose of incident radiation can be detected using conversion elements 108b, 118b. Similar to the configuration shown in FIG. 5, by dividing the conversion elements arranged in one pixel 107, 117, the areas of conversion elements 108b, 118b become smaller, and the sensitivity for detecting incident radiation decreases for each. However, as in the present disclosure, during irradiation with radiation, signals are output from conversion elements 108b, 118b arranged in two or more pixels 107, 117 to the same signal line 120 at the same timing. Thereby, during irradiation with radiation, the signal amount per one signal line 120 for obtaining irradiation information of radiation such as the incident dose can be increased for two or more conversion elements. Thereby, the accuracy of detecting the dose of incident radiation can be improved. Further, by arranging the conversion element 118b arranged in pixel 117, similar to the configuration shown in FIG. 6, a signal corresponding to the dark component of the conversion element 108b arranged in pixel 107 can be monitored. Thereby, the accuracy of correction can be improved, and the accuracy of detecting (determining) the dose of incident radiation can be enhanced.

[0068] FIG. 10 is a diagram showing a modified example of the radiation imaging apparatus 100 shown in FIG. 2. In the configuration shown in FIG. 2, the combination of pixel 104a and pixel 104b and the combination of pixel 104c and pixel 104d are connected to the same signal line 120a. However, it is not limited thereto. The combination of pixel 104a and pixel 104b may be connected to signal line 120a, and the combination of pixel 104c and pixel 104d may be connected to a signal line 120c different from signal line 120a. As shown in FIG. 10, the combination of pixel 104c and pixel 104d may be arranged adjacent to each other.

[0069] As shown in FIG. 10, the combination of pixel 104c and pixel 104d may be arranged in a pixel row different from the combination of pixel 104a and pixel 104b. In that case, a pixel row in which pixel 101 is arranged may be arranged between the pixel row in which pixel 104a and pixel 104b are arranged and the pixel row in which pixel 104c and pixel 104d are arranged, as shown in FIG. 10. Further, for example, the pixel row in which pixel 104a and pixel 104b are arranged and the pixel row in which pixel 104c and pixel 104d are arranged may be adjacent to each other.

[0070] Further, for example, the combination of pixel 104c and pixel 104d may be arranged in the same pixel row as the combination of pixel 104a and pixel 104b. In that case, pixel 104a, 104b, 104c, 104b may be connected to the same drive line 111. Also, the combination of pixel 104a and pixel 104b and the combination of pixel 104c and pixel 104d may be arranged adjacent to each other, or pixel 101 may be arranged therebetween.

[0071] Arrange them as shown in Fig. 10. By doing so, even when drive signals are supplied to drive line 111a and drive line 111b simultaneously, signals of pixel 104 corresponding to each pixel column can be separated and detected. That is, it is possible to simultaneously acquire information on the dose of radiation incident on different regions. In Fig. 10, an example where pixel 104 is arranged is shown, but pixel 107 may be arranged as shown in Figs. 5 and 9. Further, pixels 114 and 117 shown in Figs. 6 and 9 may be arranged. The above-described embodiments can be combined as appropriate.

[0072] The disclosure of this specification includes the following radiation imaging apparatus and radiation imaging system.

[0073] (Item 1) A plurality of pixels arranged in a matrix, including at least a first pixel and a second pixel, A drive circuit for controlling the plurality of pixels via a plurality of drive lines, A plurality of signal lines from which signals are output from the plurality of pixels, Comprising Each of the first pixel and the second pixel includes an image element for acquiring a radiation image and a detection element for acquiring the dose of incident radiation. The detection element arranged in the first pixel and the detection element arranged in the second pixel are connected to the same signal line among the plurality of signal lines. The drive circuit controls the detection element arranged in the first pixel and the detection element arranged in the second pixel such that the detection element arranged in the first pixel and the detection element arranged in the second pixel output signals to the same signal line at the same timing. A radiation imaging apparatus characterized by this.

[0074] (Item 2) The radiation imaging apparatus according to Item 1, characterized in that the first pixel and the second pixel are arranged adjacent to each other.

[0075] (Item 3) The radiation imaging apparatus according to claim 1 or 2, wherein the first pixel and the second pixel are arranged adjacent to each other in a direction in which the plurality of drive lines extend.

[0076] (Item 4) The radiation imaging apparatus according to any one of claims 1 to 3, wherein the detection elements respectively arranged in the first pixel and the second pixel are connected to the same drive line among the plurality of drive lines.

[0077] (Item 5) The radiation imaging apparatus according to any one of claims 1 to 4, wherein the detection elements respectively arranged in the first pixel and the second pixel are connected to drive lines different from the drive lines to which the image elements respectively arranged in the first pixel and the second pixel are connected among the plurality of drive lines.

[0078] (Item 6) The plurality of pixels further includes a third pixel and a fourth pixel, each of the third pixel and the fourth pixel includes the image element and the detection element, respectively, the detection elements arranged in the third pixel and the detection elements arranged in the fourth pixel are connected to the same signal line, During irradiation of radiation, the drive circuit controls the detection elements arranged in the third pixel and the detection elements arranged in the fourth pixel to output signals to the same signal line at the same timing. The radiation imaging apparatus according to any one of claims 1 to 5.

[0079] (Item 7) During irradiation of radiation, the drive circuit controls the detection elements respectively arranged in the first pixel, the second pixel, the third pixel, and the fourth pixel to output signals to the same signal line at the same timing. The radiation imaging apparatus according to claim 6.

[0080] (Item 8) The radiation imaging apparatus according to item 6 or 7, wherein the third pixel and the fourth pixel are arranged adjacent to each other.

[0081] (Item 9) The first pixel and the second pixel are arranged adjacent to each other in a direction in which the plurality of drive lines extend. The third pixel and the fourth pixel are arranged adjacent to each other in the extending direction. In a direction intersecting the extending direction, pixels including the image pixel among the plurality of pixels are arranged between a combination of the first pixel and the second pixel and a combination of the third pixel and the fourth pixel. The radiation imaging apparatus according to any one of items 6 to 8.

[0082] (Item 10) The plurality of pixels further includes a fifth pixel and a sixth pixel. Each of the fifth pixel and the sixth pixel includes the image pixel and the detection pixel, respectively. The detection pixel arranged in the fifth pixel and the detection pixel arranged in the sixth pixel are connected to a second signal line different from the same signal line among the plurality of signal lines. During irradiation of radiation, the drive circuit controls the detection pixel arranged in the fifth pixel and the detection pixel arranged in the sixth pixel to output signals to the second signal line at the same timing. The radiation imaging apparatus according to any one of items 1 to 9.

[0083] (Item 11) The detection pixels respectively arranged in the first pixel, the second pixel, the fifth pixel, and the sixth pixel are connected to the same drive line among the plurality of drive lines. The radiation imaging apparatus according to item 10.

[0084] (Item 12) The radiation imaging apparatus according to item 10 or 11, wherein the fifth pixel and the sixth pixel are arranged adjacent to each other.

[0085] (Item 13) The first pixel and the second pixel are arranged adjacent to each other in a direction in which the plurality of drive lines extend. The fifth pixel and the sixth pixel are arranged adjacent to each other in the extending direction. The radiation imaging apparatus according to any one of Items 10 to 12, wherein in the extending direction, a combination of the first pixel and the second pixel and a combination of the fifth pixel and the sixth pixel are arranged adjacent to each other.

[0086] (Item 14) The first pixel and the second pixel are arranged adjacent to each other in a direction in which the plurality of drive lines extend. The fifth pixel and the sixth pixel are arranged adjacent to each other in the extending direction. The radiation imaging apparatus according to any one of Items 10 to 12, wherein in the extending direction, a pixel including the image element among the plurality of pixels is arranged between a combination of the first pixel and the second pixel and a combination of the fifth pixel and the sixth pixel.

[0087] (Item 15) The apparatus further includes a processing circuit that processes signals output to the plurality of signal lines. The processing circuit before irradiation with radiation, obtains a first signal value based on signals output by the drive circuit to the detection elements respectively arranged in the first pixel and the second pixel on the same signal line at the same timing. during irradiation with radiation, corrects a second signal value corresponding to signals output by the detection elements respectively arranged in the first pixel and the second pixel to the same signal line at the same timing, using the first signal value. The radiation imaging apparatus according to any one of Items 1 to 14, wherein the dose is obtained based on the corrected second signal value.

[0088] (Item 16) Before irradiation of radiation, the drive circuit performs a first operation of resetting each of the plurality of pixels, and at least one second operation of causing the detection elements respectively arranged in the first pixel and the second pixel to output signals at the same timing. The processing circuit acquires the first signal value based on the signal obtained in the second operation, in the radiation imaging apparatus according to item 15.

[0089] (Item 17) Before a radiation start request signal is input by a user, the drive circuit starts the second operation, in the radiation imaging apparatus according to item 16.

[0090] (Item 18) In response to a radiation irradiation start request being input by a user, the drive circuit ends the first operation and starts the second operation, in the radiation imaging apparatus according to item 16.

[0091] (Item 19) Regarding the detection element as a first detection element, The plurality of pixels further includes a seventh pixel and an eighth pixel. Each of the seventh pixel and the eighth pixel includes an image element and a second detection element having a sensitivity to radiation different from that of the first detection element. The second detection element arranged in the seventh pixel and the second detection element arranged in the eighth pixel are connected to a third signal line different from the same signal line among the plurality of signal lines. The processing circuit Before irradiation of radiation, acquires a third signal value based on the signals output at the same timing to the third signal line by the drive circuit to the second detection elements respectively arranged in the seventh pixel and the eighth pixel. During irradiation of radiation, corrects a fourth signal value corresponding to the signals output at the same timing to the third signal line by the drive circuit to the second detection elements respectively arranged in the seventh pixel and the eighth pixel, using the third signal value. A radiation imaging apparatus according to any one of items 15 to 18, characterized by acquiring the dose based on the corrected second signal value and the fourth signal value respectively.

[0092] (Item 20) The radiation imaging apparatus according to item 19, wherein the first detection elements respectively arranged in the first pixel and the second pixel, and the second detection elements respectively arranged in the seventh pixel and the eighth pixel are connected to the same driving line among the plurality of driving lines.

[0093] (Item 21) The processing circuit Before irradiation with radiation, a fifth signal value acquired from the same signal line at a timing when the driving circuit does not output a signal to the first detection elements respectively arranged in the first pixel and the second pixel on the same signal line, and a sixth signal value acquired from the third signal line at a timing when the driving circuit does not output a signal to the second detection elements respectively arranged in the seventh pixel and the eighth pixel on the third signal line are further acquired. During irradiation with radiation, a seventh signal value acquired from the same signal line at a timing when the driving circuit does not output a signal to the first detection elements respectively arranged in the first pixel and the second pixel on the same signal line is corrected using the fifth signal value, and an eighth signal value acquired from the third signal line at a timing when the driving circuit does not output a signal to the second detection elements respectively arranged in the seventh pixel and the eighth pixel on the third signal line is corrected using the sixth signal value. A radiation imaging apparatus according to item 19 or 20, characterized by acquiring the dose based on the corrected second signal value, the fourth signal value, the sixth signal value, and the eighth signal value respectively.

[0094] (Item 22) The radiation imaging apparatus according to any one of items 15 to 21, wherein the processing circuit obtains the dose based on the sum of the signal values of signals output from a plurality of detection elements including the detection elements respectively arranged in the first pixel and the second pixel.

[0095] (Item 23) The plurality of pixels include a ninth pixel including the image element and not including the detection element. The radiation imaging apparatus according to any one of items 15 to 22, wherein the processing circuit further corrects the second signal value for obtaining the dose according to the difference in sensitivity to radiation between the detection elements respectively arranged in the first pixel and the second pixel and the image element arranged in the ninth pixel.

[0096] (Item 24) A plurality of pixels arranged in a matrix, including at least a first pixel and a second pixel. A drive circuit for controlling the plurality of pixels via a plurality of drive lines. A plurality of signal lines from which signals are output from the plurality of pixels. Comprising. The first pixel and the second pixel are arranged adjacent to each other in the matrix and are detection elements for detecting the dose of incident radiation, and each includes a detection element connected to the same signal line among the plurality of signal lines. The drive circuit controls the detection element arranged in the first pixel and the detection element arranged in the second pixel so that the detection element arranged in the first pixel and the detection element arranged in the second pixel output signals to the same signal line at the same timing. The radiation imaging apparatus is characterized by this.

[0097] (Item 25) A radiation imaging apparatus according to any one of items 1 to 24. A signal processing unit that processes a signal output from the radiation imaging apparatus. A radiation imaging system characterized by comprising.

[0098] The invention is not limited to the above embodiments, and various changes and modifications can be made without departing from the spirit and scope of the invention. Therefore, the claims are appended to disclose the scope of the invention.

Explanation of Reference Numerals

[0099] 100: Radiation imaging device, 101, 104, 107: Pixel, 110, 111: Driving line, 120: Signal line, 150: Driving circuit

Claims

1. A plurality of pixels arranged in a matrix, the plurality of pixels including at least a first pixel and a second pixel, a driving circuit that controls the plurality of pixels via a plurality of driving lines, a plurality of signal lines from which signals are output from the plurality of pixels, and comprising, each of the first pixel and the second pixel includes an image element for acquiring a radiation image and a detection element for acquiring the dose of incident radiation, the detection element arranged in the first pixel and the detection element arranged in the second pixel are connected to the same signal line among the plurality of signal lines, the driving circuit is configured to control the detection element arranged in the first pixel and the detection element arranged in the second pixel such that the detection element arranged in the first pixel and the detection element arranged in the second pixel output signals to the same signal line at the same timing. A radiation imaging apparatus characterized by that.

2. The radiation imaging apparatus according to claim 1, wherein the first pixel and the second pixel are arranged adjacent to each other.

3. The radiation imaging apparatus according to claim 1, wherein the first pixel and the second pixel are arranged adjacent to each other in a direction in which the plurality of driving lines extend.

4. The radiation imaging apparatus according to claim 1, wherein the detection elements respectively arranged in the first pixel and the second pixel are connected to the same driving line among the plurality of driving lines.

5. The radiation imaging apparatus according to claim 1, wherein the detection elements respectively arranged in the first pixel and the second pixel are connected to a driving line different from the driving line to which the image elements respectively arranged in the first pixel and the second pixel are connected among the plurality of driving lines.

6. The plurality of pixels further includes a third pixel and a fourth pixel, each of the third pixel and the fourth pixel includes the image element and the detection element respectively, the detection element arranged in the third pixel and the detection element arranged in the fourth pixel are connected to the same signal line, during irradiation with radiation, the driving circuit is configured to control the detection element arranged in the third pixel and the detection element arranged in the fourth pixel such that the detection element arranged in the third pixel and the detection element arranged in the fourth pixel output signals to the same signal line at the same timing. A radiation imaging apparatus according to claim 1, characterized by that.

7. During the irradiation of radiation, the drive circuit controls the detection elements respectively arranged in the first pixel, the second pixel, the third pixel, and the fourth pixel to output signals to the same signal line at the same timing. The radiation imaging apparatus according to claim 6, characterized in that.

8. The radiation imaging apparatus according to claim 6, characterized in that the third pixel and the fourth pixel are arranged adjacent to each other.

9. The first pixel and the second pixel are arranged adjacent to each other in the direction in which the plurality of drive lines extend. The third pixel and the fourth pixel are arranged adjacent to each other in the extending direction. In a direction intersecting the extending direction, between the combination of the first pixel and the second pixel and the combination of the third pixel and the fourth pixel, pixels including the image elements among the plurality of pixels are arranged. The radiation imaging apparatus according to claim 6, characterized in that.

10. The plurality of pixels further include a fifth pixel and a sixth pixel. Each of the fifth pixel and the sixth pixel includes the image element and the detection element respectively. The detection element arranged in the fifth pixel and the detection element arranged in the sixth pixel are connected to a second signal line different from the same signal line among the plurality of signal lines. During the irradiation of radiation, the drive circuit controls the detection element arranged in the fifth pixel and the detection element arranged in the sixth pixel to output signals to the second signal line at the same timing. The radiation imaging apparatus according to claim 1, characterized in that.

11. The radiation imaging apparatus according to claim 10, characterized in that the detection elements respectively arranged in the first pixel, the second pixel, the fifth pixel, and the sixth pixel are connected to the same drive line among the plurality of drive lines.

12. The radiation imaging apparatus according to claim 10, characterized in that the fifth pixel and the sixth pixel are arranged adjacent to each other.

13. The first pixel and the second pixel are arranged adjacent to each other in the direction in which the plurality of drive lines extend. The fifth pixel and the sixth pixel are arranged adjacent to each other in the extending direction. The radiation imaging apparatus according to claim 10, wherein in the extending direction, a combination of the first pixel and the second pixel and a combination of the fifth pixel and the sixth pixel are arranged adjacent to each other.

14. The first pixel and the second pixel are arranged adjacent to each other in a direction in which the plurality of drive lines extend. The fifth pixel and the sixth pixel are arranged adjacent to each other in the extending direction. The radiation imaging apparatus according to claim 10, wherein in the extending direction, a pixel including the image element among the plurality of pixels is arranged between a combination of the first pixel and the second pixel and a combination of the fifth pixel and the sixth pixel.

15. The apparatus further includes a processing circuit that processes signals output to the plurality of signal lines. The processing circuit before irradiation with radiation, acquires a first signal value based on signals output by the drive circuit to the detection elements respectively arranged in the first pixel and the second pixel on the same signal line at the same timing. during irradiation with radiation, corrects a second signal value corresponding to signals output by the detection elements respectively arranged in the first pixel and the second pixel to the same signal line at the same timing, using the first signal value. The radiation imaging apparatus according to claim 1, wherein the dose is acquired based on the corrected second signal value.

16. Before irradiation with radiation, the drive circuit performs a first operation of resetting each of the plurality of pixels and at least one second operation of outputting signals to the detection elements respectively arranged in the first pixel and the second pixel at the same timing. The radiation imaging apparatus according to claim 15, wherein the processing circuit acquires the first signal value based on the signals obtained in the second operation.

17. The radiation imaging apparatus according to claim 16, wherein the drive circuit starts the second operation before a radiation start request signal is input by a user.

18. The radiation imaging apparatus according to claim 16, wherein in response to a radiation irradiation start request input by a user, the drive circuit ends the first operation and starts the second operation.

19. Taking the detection element as a first detection element, the plurality of pixels further include a seventh pixel and an eighth pixel. Each of the seventh pixel and the eighth pixel includes the image element and a second detection element having a sensitivity to radiation different from that of the first detection element. The second detection element disposed in the seventh pixel and the second detection element disposed in the eighth pixel are connected to a third signal line different from the same signal line among the plurality of signal lines. The processing circuit Before irradiation with radiation, the driving circuit acquires a third signal value based on a signal output to the second detection elements respectively disposed in the seventh pixel and the eighth pixel on the third signal line at the same timing. During irradiation with radiation, the driving circuit corrects a fourth signal value corresponding to the signal output to the second detection elements respectively disposed in the seventh pixel and the eighth pixel on the third signal line at the same timing, using the third signal value. The radiation imaging apparatus according to claim 15, wherein the dose is acquired based on the corrected second signal value and the fourth signal value respectively.

20. The radiation imaging apparatus according to claim 19, wherein the first detection elements respectively disposed in the first pixel and the second pixel, and the second detection elements respectively disposed in the seventh pixel and the eighth pixel are connected to the same driving line among the plurality of driving lines.

21. The processing circuit Before irradiation with radiation, the processing circuit further acquires a fifth signal value obtained from the same signal line at a timing when the driving circuit does not output a signal to the first detection elements respectively disposed in the first pixel and the second pixel on the same signal line, and a sixth signal value obtained from the third signal line at a timing when the driving circuit does not output a signal to the second detection elements respectively disposed in the seventh pixel and the eighth pixel on the third signal line. During irradiation with radiation, the processing circuit corrects a seventh signal value obtained from the same signal line at a timing when the driving circuit does not output a signal to the first detection elements respectively disposed in the first pixel and the second pixel on the same signal line, using the fifth signal value, and corrects an eighth signal value obtained from the third signal line at a timing when the driving circuit does not output a signal to the second detection elements respectively disposed in the seventh pixel and the eighth pixel on the third signal line, using the sixth signal value. The radiation imaging apparatus according to claim 19, wherein the dose is obtained based on the respectively corrected second signal value, the fourth signal value, the sixth signal value, and the eighth signal value.

22. The radiation imaging apparatus according to claim 15, wherein the processing circuit obtains the dose based on the sum of the signal values of signals output from a plurality of detection elements including the detection elements respectively arranged in the first pixel and the second pixel.

23. The plurality of pixels include a ninth pixel that includes the image element and does not include the detection element. The radiation imaging apparatus according to claim 15, wherein the processing circuit further corrects the second signal value for obtaining the dose according to a difference in sensitivity to radiation between the detection elements respectively arranged in the first pixel and the second pixel and the image element arranged in the ninth pixel.

24. A plurality of pixels arranged in a matrix, including at least a plurality of pixels including a first pixel and a second pixel. A drive circuit that controls the plurality of pixels via a plurality of drive lines. A plurality of signal lines from which signals are output from the plurality of pixels. Comprising The first pixel and the second pixel are arranged adjacent to each other in the matrix and are detection elements for detecting the dose of incident radiation, and each includes a detection element connected to the same signal line among the plurality of signal lines. The radiation imaging apparatus, wherein the drive circuit controls the detection element arranged in the first pixel and the detection element arranged in the second pixel so that the detection element arranged in the first pixel and the detection element arranged in the second pixel output signals to the same signal line at the same timing.

25. A radiation imaging system, comprising: the radiation imaging apparatus according to any one of claims 1 to 24; A signal processing unit that processes a signal output from the radiation imaging apparatus. Characterized by comprising.

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