JP6195967B2 - Radiation image capturing apparatus, radiation image capturing system, control program for radiation image capturing apparatus, and control method for radiation image capturing apparatus - Google Patents

Description

  The present invention relates to a radiographic image capturing apparatus, a radiographic image capturing system, a control program for the radiographic image capturing apparatus, and a control method for the radiographic image capturing apparatus, and in particular, a radiographic image used for capturing a radiographic image corresponding to the irradiated radiation. The present invention relates to an imaging apparatus, a radiographic imaging system, a control program for the radiographic imaging apparatus, and a control method for the radiographic imaging apparatus.

  2. Description of the Related Art Conventionally, a radiographic imaging apparatus that performs radiography for medical diagnosis and the like is known. The radiation image capturing apparatus captures a radiation image by detecting radiation irradiated from the radiation irradiation apparatus and transmitted through the subject. The radiographic image capturing apparatus captures a radiographic image by collecting and reading out charges generated according to the irradiated radiation. An example of such a radiographic imaging apparatus is an FPD (Flat Panel Detector) panel such as a so-called cassette.

  As such a radiographic imaging apparatus, a radiation detection element such as a photoelectric conversion element that generates charges in response to radiation or radiation detected by irradiation with radiation-converted radiation, and generated by the radiation detection element And a switch element for reading the generated charge, and a detector having a detection unit for detecting radiation irradiation (irradiation start, stop, etc.) based on the charge read from the switch element. Yes. For example, Patent Document 1 describes an X-ray imaging apparatus that includes a notification unit that notifies the driving state of a detector that detects X-rays without requiring synchronization with the generation timing of X-rays.

  When a radiographic image is taken with such a radiographic imaging device, an electrical signal is generated due to disturbance noise such as impact or electromagnetic waves, and the radiographic image is abnormal due to the electrical signal. May occur.

  Therefore, there is a technique for detecting the presence or absence of noise. For example, in Patent Document 2, a noise detection unit is provided separately from a radiation detection unit (pixel) that detects radiation, and is generated by the radiation detection unit (pixel) when it is determined that there is no noise based on an electrical signal. A technique for reading out a charge and taking a radiographic image is described.

JP 2010-264250 A JP 2004-24683 A

  However, in the above conventional technique, there is a concern that the presence or absence of noise is erroneously detected when the timing of generation of noise and radiation exposure are close. In such a case, there is a concern that the occurrence of noise is not properly notified to the user.

  The present invention has been made in order to solve the above-described problems, and is capable of appropriately detecting and notifying the presence or absence of noise during radiographic image capturing, and a radiographic image capturing apparatus and radiographic image capturing system. An object of the present invention is to provide a control program for a radiographic imaging apparatus and a control method for radiographic imaging.

In order to achieve the above object, the radiographic imaging device of the present invention generates a charge according to the dose of irradiated radiation, reads out the charge generated in the sensor unit that accumulates the generated charge, and the sensor unit. A plurality of pixels each provided with a switch element to be output to the signal wiring, and a detection means for detecting the start of irradiation when an electrical signal corresponding to the charge generated by radiation irradiation satisfies a predetermined irradiation detection condition; after detecting the start of irradiation by the detection means, an electrical signal Tokushi preparative an electric signal corresponding to the charges read out from the pixel, the electric signal is judged whether comprising an electrical signal caused by noise, due to the noise Control means for controlling the notification means so as to be notified.

The radiation imaging apparatus of the present invention, after detecting the start of irradiation by the detection means, the control means, the sensor unit to start accumulation of charge, the electric signal the electrical signal after the accumulation start is that attributable to noise It may be judged whether it is included.

In addition, the control means of the radiographic imaging device of the present invention detects the electrical signal acquired after detecting the start of radiation irradiation by the detection means, the condition predetermined for noise intensity detection, and the noise generation period detection. based a predetermined condition, to the, to detect the intensity and period of generation of noise, based on the detected intensity and generation period, but it may also be determined whether to output the radiation image.

The control unit of the radiation image capturing apparatus of the present invention, if at least one of when it is detected that the case and generation period is detected that intensity of the noise is weak is short, determine to output the radiation image Also good.

Further, the control means of the radiographic imaging device of the present invention may determine that no radiographic image is output when it is detected that the noise intensity is strong and the noise generation period is long.

In addition, the control unit of the radiographic image capturing apparatus of the present invention acquires an electrical signal corresponding to the charge for each predetermined region according to the plurality of pixels, and the electrical signal becomes noise for each predetermined region. It may be determined whether the resulting electrical signal is included.

The control unit of the radiation image capturing apparatus of the present invention may notify the predetermined area is determined that the electric signal is Ru included due to noise.

The control unit of the radiation image capturing apparatus of the present invention, based on the predetermined area of the position determining that noise Ru contains an electric signal due to, to determine whether to output the radiation image Also good.

The control unit of the radiation image capturing apparatus of the present invention, when the position of the predetermined region is determined that Ru contains an electric signal due to noise, a predetermined position as the central to the entire region It may be determined that no radiation image is output.

The control unit of the radiation image capturing apparatus of the present invention is based on the time variation of the obtained electrical signals, if the electrical signal exceeds the noise detection threshold, it is determined to contain an electrical signal due to the noise May be.

The control unit of the radiation image capturing apparatus of the present invention is based on the electrical signal obtained by differentiating processing a temporal change in the acquired electrical signal, when the electrical signal exceeds a noise threshold value for detecting an electrical to attributable to noise It may be determined that a signal is included.

The control unit of the radiation image capturing apparatus of the present invention is based on the time variation of the obtained electrical signals, time moving average is calculated, based on the difference between an electrical signal at a point determines that the moving average calculated time When the difference exceeds the noise detection threshold, it may be determined that an electric signal caused by noise is included.

Further, the control means of the radiographic image capturing apparatus of the present invention may detect the intensity of noise by comparing the acquired electrical signal with an intensity detection threshold value .

Further, the control means of the radiographic imaging apparatus of the present invention may detect the noise generation period based on the number of times the acquired electrical signal has reached the generation time detection threshold.
Moreover, the alerting | reporting means of the radiographic imaging apparatus of this invention may be provided in the radiographic image detector containing a some pixel .
Moreover, the notification means of the radiographic imaging device of the present invention may be provided outside a radiographic image detector having a plurality of pixels .
In addition, the plurality of pixels of the radiographic image capturing apparatus of the present invention include a radiographic image capturing pixel and a radiation detection pixel, and the detection means performs radiation based on an electrical signal corresponding to the electric charge output from the radiation detection pixel. The control unit may acquire an electrical signal corresponding to the electric charge read from the radiation detection pixel .
The switch element of the radiation image capturing pixels of the radiographic image capturing apparatus of the present invention outputs a charge to the signal lines based on the control signal, the radiation detection pixels, the charge to the signal line regardless of the control signal It may be output.
The radiation detection pixels of the radiographic image capturing apparatus of the present invention, based on the control signal flowing through switching elements of the radiation image capturing driven based on a control signal through the first scan line, and a second scan line The detection means includes a radiation detection switch element that is driven, and the detection means detects the start of radiation irradiation based on an electrical signal corresponding to the electric charge read out by driving the radiation detection switch element . An electrical signal corresponding to the electric charge read from the radiation detection pixel and an electric signal corresponding to the electric charge read by driving the radiation image capturing switch element of the radiation detection pixel may be acquired.
Further, radiographic imaging pixels of the radiographic imaging apparatus of the present invention, a radiographic imaging for the switch element, and includes a switching element for radiation detection, switching elements for radiation detection, a non-connected to the signal line There may be.
The radiation imaging apparatus of the present invention comprises a bias voltage applied from a bias power source and a bias line for supplying the sensor part of the multiple pixels, a charge detecting means for detecting the charge flowing to the bias line, the The detecting means may detect the start of radiation irradiation based on the change in the charge detected by the charge detecting means .
The radiation imaging apparatus of the present invention, between the detection phase detection means detects the start of irradiation of radiation, the switching element may be turned off.
The detection period in the radiographic imaging apparatus of the present invention interrupts the irradiation start of the detection of the radiation at every predetermined time, outputs the switching element in the ON state, reads out the charges generated by the sensor unit to the signal line Then, the switch element may be turned off and detection of the start of radiation irradiation may be resumed.
Further, the predetermined irradiation detection conditions in the radiation imaging apparatus of the present invention may be a predetermined condition by a threshold for output radiation detection.
Further, the control means of the radiographic image capturing apparatus of the present invention acquires an electrical signal corresponding to the electric charge read from the pixel for each predetermined region according to the plurality of pixels, and for each predetermined region. It is determined whether the electric signal includes an electric signal due to noise, and when the electric signal includes the electric signal due to noise, the radiographic image and information regarding a predetermined region determined to include the electric signal due to noise ; may further perform association with internal or external Ru control is stored on at least one of its own device.
The radiation imaging apparatus of the present invention further comprises an amplifier for sampling the electrical signals corresponding to the charges read from the sensor unit, after detecting the start of irradiation by the detection means, the control means, sensor parts to initiate the accumulation of charge, the electric signal after the start of the accumulation to determine whether including the electrical signal to be attributable to noise, when it is determined to include an electrical signal due to noise, which is sampled in the amplifier charges May be reset, and the detection means may again start detecting the start of radiation irradiation .
Further, in the radiographic imaging device of the present invention, after the detection unit detects the start of radiation irradiation, the control unit causes the sensor unit to start accumulating electric charges, and the electric signal is caused by noise after the accumulation starts. If it is determined whether or not an electric signal caused by noise is included, shooting may be stopped.
Further, in the radiographic imaging device of the present invention, after the detection unit detects the start of radiation irradiation, the control unit causes the sensor unit to start accumulating electric charges, and the electric signal is caused by noise after the accumulation starts. If it is determined that an electrical signal caused by noise is included, radiation irradiation may be stopped.
In order to achieve the above object, a radiographic imaging system of the present invention includes a radiation irradiating apparatus and a radiographic imaging apparatus of the present invention that captures a radiographic image with radiation irradiated from the radiation irradiating apparatus .
In order to achieve the above object, a control program of the radiographic imaging apparatus of the present invention is to generate charge in response to the irradiated radiation sensor portion for accumulating the generated electric charges, and the charge that occurred by the sensor unit a plurality of pixels having each a switching element that outputs the signal wiring reads, release the start of irradiation of radiation to the radiation detecting satisfies field if the electrical signal is predetermined in accordance with the generated charges upon irradiation with rays After detecting the start of radiation irradiation by the detection means, an electric signal corresponding to the electric charge read from the pixel is acquired, and it is determined whether the electric signal includes an electric signal due to noise. , when including an electrical signal due to noise, the radiographic image capturing apparatus having a control means for controlling the informing hands stage to broadcast, and is for causing a computer to function as the control means
To achieve the above object, a control method of a radiographic imaging apparatus of the present invention is to generate charge in response to irradiated Radiation sensor unit for accumulating the generated electric charges, and the charges generated by the sensor unit when read out radiographic image by a radiation ray imaging apparatus having a plurality of pixels having each a switching element that outputs the signal wiring, the electrical signal corresponding to the charges generated by irradiation of radiation predetermined a detection step for detecting the start of irradiation when irradiation detection condition is satisfied, after detecting the start of irradiation in the detection step, and obtains the electrical signal depending on the charges read from the pixels, the electric A control step of determining whether the signal includes an electrical signal due to noise and controlling the notification means so as to be notified when the signal includes an electrical signal due to noise .

  As described above, there is an effect that it is possible to appropriately detect and notify the presence or absence of noise at the time of radiographic image capturing.

It is a schematic structure figure showing a schematic structure of an example of a radiographic imaging system concerning a 1st embodiment. It is a block diagram which shows an example of the whole structure of the radiographic image detector which concerns on 1st Embodiment. It is explanatory drawing for demonstrating the external appearance of the radiation detector which concerns on 1st Embodiment. It is a top view which shows an example of a structure of the radiation detector which concerns on 1st Embodiment. It is a line sectional view of an example of a radiation detector concerning a 1st embodiment. It is a line sectional view of an example of a radiation detector concerning a 1st embodiment. It is a flowchart of an example of the imaging process of a radiographic image in the radiographic imaging apparatus which concerns on 1st Embodiment. It is explanatory drawing for demonstrating the electrical signal according to the irradiated radiation. It is explanatory drawing for demonstrating noise, (A) shows alternating current noise and (B) has shown rectangular noise. It is a flowchart of an example of the signal analysis process in the radiographic imaging device which concerns on 1st Embodiment. It is explanatory drawing for demonstrating the profile of the time change of the intensity | strength before performing the differentiation process performed in 1st Embodiment, (A) shows the case where noise is not included, (B) Indicates a case where AC noise having a high intensity and a short generation period is generated, and (C) indicates a case where AC noise having a high intensity and a long generation period is generated. It is explanatory drawing for demonstrating the profile of the time change of the intensity | strength after the differentiation process performed in 1st Embodiment was performed, (A) shows the case where noise is not included, (B ) Shows a case where AC noise having a high intensity and a short generation period is generated, and (C) shows a case where AC noise having a high intensity and a long generation period is generated. It is explanatory drawing for demonstrating a specific example of the determination of the noise of this Embodiment. It is a flowchart of an example of the signal analysis process in the radiographic imaging device which concerns on 1st Embodiment. It is explanatory drawing for demonstrating the profile of the time change of the intensity | strength after the differentiation process performed in 2nd Embodiment was performed, (A) shows the case where noise is not included, (B ) Shows a case where AC noise having a high intensity and a short generation period is generated, and (C) shows a case where AC noise having a high intensity and a long generation period is generated. It is a block diagram which shows an example of the whole structure of the radiographic image detector which concerns on 3rd Embodiment. It is a flowchart of an example of the imaging process of a radiographic image in the radiographic imaging apparatus which concerns on 3rd Embodiment. It is a flowchart of an example of the signal analysis process in the radiographic imaging device which concerns on 3rd Embodiment. It is explanatory drawing for demonstrating the external appearance of the radiation detector which concerns on 3rd Embodiment. It is a flowchart of an example of the radiographic image display principle in the control apparatus of the radiographic imaging device which concerns on 3rd Embodiment. It is explanatory drawing for demonstrating a specific example of the display of the radiographic image which concerns on 3rd Embodiment. It is a flowchart of an example of the imaging process of a radiographic image in the radiographic imaging apparatus which concerns on 4th Embodiment. It is a block diagram which shows an example of the whole structure of the radiographic image detector which concerns on 5th Embodiment. It is a block diagram which shows another example of the whole structure of the radiographic image detector which concerns on 5th Embodiment. It is a flowchart of an example of a radiation irradiation start detection process in the radiographic imaging device which concerns on 5th Embodiment. It is a block diagram which shows an example of the whole structure of the radiographic image detector which concerns on 6th Embodiment. It is a flowchart of an example of a radiation irradiation start detection process in the radiographic imaging device which concerns on 6th Embodiment. It is a block diagram which shows an example of the whole structure of the radiographic image detector which concerns on 7th Embodiment. It is a flowchart of an example of the imaging process of a radiographic image in the radiographic imaging apparatus which concerns on 7th Embodiment.

  Hereinafter, an example of the present embodiment will be described with reference to the drawings.

[First Embodiment]
First, a schematic configuration of a radiographic imaging system using the radiographic imaging apparatus of the present embodiment will be described. FIG. 1 is a schematic configuration diagram of an example of a radiographic image capturing system according to the present embodiment.

  The radiographic image capturing system 200 includes a radiation irradiation device 204 that irradiates a subject 206 with radiation (for example, X-ray (X-ray) or the like), and a radiographic image capturing device 201. The radiographic image capturing apparatus 201 instructs the radiographic image detector 100 including the radiation image detector 100 including the radiation detector 10 that detects the radiation irradiated from the radiation irradiating apparatus 204 and transmitted through the subject 206 to the radiographic image. And a control device 202 that acquires a radiation image from the detector 100. At a timing based on the control of the control device 202, the radiation carrying the image information by passing through the subject 206 irradiated from the radiation irradiation device 204 and positioned at the imaging position is irradiated to the radiation image detector 100.

  The control device 202 includes a control unit 210, a display unit 212, and a notification unit 213. The control unit 210 has a function of controlling the entire control device 202 and the radiation image capturing device 201, and is configured by a microcomputer. The control unit 210 includes a nonvolatile storage unit including a CPU (Central Processing Unit), ROM and RAM, flash memory, and the like. The control unit 210 performs the above-described control by executing a program stored in the ROM by the CPU. The display unit 212 is, for example, a display, a liquid crystal, and the like, and has a function of displaying a captured radiographic image, displaying information related to radiographic image capturing (including information related to noise, which will be described in detail later), and the like. If it has, it will not specifically limit. Although the details will be described later, the notification unit 213 has a function of notifying the user when the radiation image detector 100 noise is detected. For example, the notification unit 213 is provided separately from the speaker and the display unit 212. Display devices, LEDs, and the like, which are not particularly limited. Moreover, in the control apparatus 202, when the information regarding the detection of noise is displayed only on the display unit 212, the notification unit 213 may not be provided.

  Next, a schematic configuration of the radiation image detector 100 according to the present embodiment will be described. FIG. 2 is a configuration diagram showing an example of the overall configuration of the radiation image detector 100 according to the present embodiment. In the present embodiment, a case will be described in which the present invention is applied to an indirect conversion radiation detector 10 that once converts radiation such as X-rays into light and converts the converted light into electric charges. In the present embodiment, the radiation image detector 100 includes the radiation detector 10 of an indirect conversion method. In FIG. 2, a scintillator that converts radiation into light is omitted.

  The radiation detector 10 includes a sensor unit 103 that receives light to generate charges, accumulates the generated charges, and a TFT switch 4 that is a switch element for reading out the charges accumulated in the sensor unit 103. A plurality of pixels 20 are arranged in a matrix. In this embodiment mode, charges are generated in the sensor unit 103 by irradiation with light converted by the scintillator.

  A plurality of pixels 20 are arranged in a matrix in one direction (scanning line direction in FIG. 2, hereinafter also referred to as “row direction”) and a crossing direction with respect to the row direction (signal wiring direction in FIG. 2, hereinafter also referred to as “column direction”). Has been placed. In FIG. 2, the arrangement of the pixels 20 is shown in a simplified manner. For example, 1024 × 1024 pixels 20 are arranged in the row direction and the column direction.

  In the present embodiment, among the plurality of pixels 20, a radiation image capturing pixel 20 </ b> A and a radiation detection pixel 20 </ b> B are determined in advance. In FIG. 1, the radiation detection pixel 20 </ b> B is surrounded by a broken line. The radiation image capturing pixel 20A is used to detect radiation and generate an image indicated by the radiation, and the radiation detection pixel 20B is a pixel used to detect radiation. It is a pixel that outputs electric charges regardless of on / off (details will be described later).

  The radiation detector 10 includes a plurality of scanning wirings 101 for turning on / off the TFT switch 4 and a plurality of charges for reading out the charges accumulated in the sensor unit 103 on the substrate 1 (see FIG. 4). The signal wirings 3 are provided so as to cross each other. In the present embodiment, one signal wiring 3 is provided for each pixel column in one direction, and one scanning wiring 101 is provided for each pixel column in the intersecting direction. When 1024 × 1024 are arranged in the column direction, 1024 signal wirings 3 and scanning wirings 101 are provided.

  Further, the radiation detector 10 is provided with a bias line 25 in parallel with each signal wiring 3. One end and the other end of the bias line 25 are connected in parallel, and one end is connected to the power supply 110 that supplies a predetermined bias voltage. The sensor unit 103 is connected to the bias line 25, and a bias voltage is applied via the bias line 25.

  A drive signal for switching each TFT switch 4 flows through the scanning wiring 101. Thus, each TFT switch 4 is switched by the drive signal flowing through each scanning wiring 101.

  When the TFT switch 4 of each pixel 20 is in an on state, an electric signal corresponding to the electric charge accumulated in each pixel 20 flows through the signal wiring 3. More specifically, an electrical signal corresponding to the amount of charge accumulated by turning on any TFT switch 4 of the pixel 20 connected to the signal wiring 3 flows to each signal wiring 3.

  Each signal wiring 3 is connected to a signal detection circuit 105 that detects an electrical signal flowing out to each signal wiring 3. Further, each scanning wiring 101 is connected to a scanning wiring driving circuit 104 that outputs a driving signal for turning on / off the TFT switch 4 to each scanning wiring 101. In FIG. 2, the signal detection circuit 105 and the scanning wiring driving circuit 104 are shown in a simplified form. However, for example, a plurality of signal detection circuits 105 and scanning wiring driving circuits 104 are provided (for example, 256). The signal wiring 3 or the scanning wiring 101 is connected every time. For example, when 1024 signal wirings 3 and 1024 scanning wirings 101 are provided, four scanning wiring driving circuits 104 are provided to connect 256 scanning wirings 101, and four signal detection circuits 105 are provided to 256 wirings. The signal wiring 3 is connected one by one.

  The signal detection circuit 105 includes an amplification circuit 50 that amplifies an input electric signal for each signal wiring 3. In the signal detection circuit 105, the electric signal input from each signal wiring 3 is amplified by the amplification circuit 50 and output to the A / D (analog / digital) conversion circuit 54.

  The amplifier circuit 50 includes a charge amplifier circuit, and includes an amplifier 52 such as an operational amplifier, a capacitor C connected in parallel to the amplifier 52, and a charge reset switch SW1 connected in parallel to the amplifier 52. It is prepared for.

  In the amplifier circuit 50, the charge (electric signal) is read out by the TFT switch 4 of the pixel 20 with the charge reset switch SW1 being off, and the charge read out by the TFT switch 4 is stored in the capacitor C. The voltage value output from the amplifier 52 increases in accordance with the amount of charge that is generated.

  The control unit 106 applies a charge reset signal to the charge reset switch SW1 to control on / off of the charge reset switch SW1. When the charge reset switch SW1 is turned on, the input side and output side of the amplifier 52 are short-circuited, and the capacitor C is discharged.

  The A / D conversion circuit 54 has a function of converting an electrical signal, which is an analog signal input from the amplifier circuit 50, into a digital signal when the S / H (sample hold) switch SW of the signal detection circuit 105 is in an ON state. It is. The A / D conversion circuit 54 sequentially outputs the electrical signals converted into digital signals to the control unit 106.

  Note that the A / D conversion circuit 54 of the present embodiment receives electric signals output from all the amplification circuits 50 provided in the signal detection circuit 105. That is, the signal detection circuit 105 of the present embodiment includes one A / D conversion circuit 54 regardless of the number of amplifier circuits 50 (signal wirings 3).

  A control unit 106 is connected to the signal detection circuit 105 and the scanning wiring drive circuit 104. The control unit 106 according to the present embodiment is configured by a microcomputer, and includes a nonvolatile storage unit including a CPU (Central Processing Unit), a ROM and a RAM, a flash memory, and the like. The control unit 106 performs control for radiographic imaging by executing a program stored in the ROM by the CPU.

  The control unit 106 according to the present embodiment performs predetermined processing such as noise removal on the digital signal converted by the signal detection circuit 105, detects the start of radiation irradiation, and based on the detected timing, It has a function of outputting a control signal indicating the timing of signal detection to the signal detection circuit 105 and outputting a control signal indicating the timing of output of the drive signal to the scanning wiring driving circuit 104. Further, after detecting the start of radiation irradiation, the control unit 106 according to the present embodiment determines whether the electrical signal is caused by noise or radiation based on the electrical signal read from the pixel 20B. It has a function to determine whether to do.

  In addition, the control unit 106 performs processing (interpolation processing) for interpolating the image data of each radiation detection pixel 20B on the image data on which the predetermined processing has been performed, and the image indicated by the irradiated radiation Is generated. That is, the control unit 106 generates a radiation image indicated by the irradiated radiation by interpolating the image data of each radiation detection pixel 20B based on the image data subjected to the predetermined processing.

  In addition, the radiation image detector 100 according to the present embodiment includes a notification unit 108. When the control unit 106 determines that the notification unit 108 is an electric signal due to noise, the notification unit 108 has a function of notifying a user who takes a radiographic image to that effect. Although the structure of the alerting | reporting part 108 is not specifically limited, For example, the speaker for alerting | reporting with LED for performing a visual display, a sound, etc. are mentioned.

  The radiation image detector 100 according to the present embodiment includes the above-described radiation detector 10, the A / D conversion circuit 54, the scanning wiring drive circuit 104, the control unit 106, the signal detection circuit 105, the bias power supply 110, and the like. 120. FIG. 3 shows the appearance of the housing 120. FIG. 3A shows a specific example when the notification unit 108 is an LED, and FIG. 3B shows a specific example when the notification unit 108 is a speaker. As described above, the notification unit 108 is provided at a position (for example, a side surface) where the radiation is not irradiated on the housing 120 and is easily recognized by the user.

  FIG. 4 is a plan view showing the structure of the radiation detector 10 of the indirect conversion type according to the present embodiment, and FIG. 5 shows an AA line of the radiographic image capturing pixel 20A of FIG. A cross-sectional view is shown, and FIG. 6 shows a cross-sectional view taken along line B-B of the radiation detection pixel 20 </ b> B of FIG. 4.

  As shown in FIG. 5, the pixel 20 </ b> A of the radiation detector 10 has a scanning wiring 101 (see FIG. 4) and a gate electrode 2 formed on an insulating substrate 1 made of non-alkali glass or the like. 101 and the gate electrode 2 are connected (see FIG. 4). The wiring layer in which the scanning wiring 101 and the gate electrode 2 are formed (hereinafter, this wiring layer is also referred to as “first signal wiring layer”) uses Al or Cu, or a laminated film mainly composed of Al or Cu. Although formed, it is not limited to these.

An insulating film 15 is formed on one surface of the first signal wiring layer, and a portion located on the gate electrode 2 functions as a gate insulating film in the TFT switch 4. The insulating film 15 is made of, for example, SiN _X or the like, and is formed by, for example, CVD (Chemical Vapor Deposition) film formation.

  On the gate electrode 2 on the insulating film 15, the semiconductor active layer 8 is formed in an island shape. The semiconductor active layer 8 is a channel portion of the TFT switch 4 and is made of, for example, an amorphous silicon film.

  A source electrode 9 and a drain electrode 13 are formed on these upper layers. In the wiring layer in which the source electrode 9 and the drain electrode 13 are formed, the signal wiring 3 is formed together with the source electrode 9 and the drain electrode 13. The source electrode 9 is connected to the signal wiring 3 (see FIG. 4). The wiring layer in which the source electrode 9, the drain electrode 13, and the signal wiring 3 are formed (hereinafter, this wiring layer is also referred to as “second signal wiring layer”) is a laminate mainly composed of Al or Cu, or Al or Cu. The film is formed using, but is not limited to these. Between the source electrode 9 and the drain electrode 13 and the semiconductor active layer 8, an impurity-added semiconductor layer (not shown) made of impurity-added amorphous silicon or the like is formed. These constitute the TFT switch 4 for switching. In the TFT switch 4, the source electrode 9 and the drain electrode 13 are reversed depending on the polarity of charges collected and accumulated by the lower electrode 11 described later.

A TFT protective film layer 30 is provided to cover the second signal wiring layer and to protect the TFT switch 4 and the signal wiring 3 over almost the entire area (substantially the entire area) where the pixel 20 is provided on the substrate 1. Is formed. The TFT protective film layer 30 is made of, for example, SiN _X or the like, and is formed by, for example, CVD film formation.

  A coating type interlayer insulating film 12 is formed on the TFT protective film layer 30. The interlayer insulating film 12 is a photosensitive organic material having a low dielectric constant (relative dielectric constant εr = 2 to 4) (for example, a positive photosensitive acrylic resin: a base made of a copolymer of methacrylic acid and glycidyl methacrylate). It is formed with a film thickness of 1 to 4 μm by a material obtained by mixing a polymer with a naphthoquinonediazide positive photosensitive agent.

  In the radiation detector 10 according to the present exemplary embodiment, the interlayer insulating film 12 suppresses the capacitance between metals disposed in the upper and lower layers of the interlayer insulating film 12 to be low. In general, such a material also has a function as a flattening film, and has an effect of flattening a lower step. In the radiation detector 10 according to the present exemplary embodiment, a contact hole 17 is formed at a position facing the drain electrode 13 of the interlayer insulating film 12 and the TFT protective film layer 30.

  A lower electrode 11 of the sensor unit 103 is formed on the interlayer insulating film 12 so as to cover the pixel region while filling the contact hole 17, and the lower electrode 11 is connected to the drain electrode 13 of the TFT switch 4. ing. If the semiconductor layer 21 described later is as thick as about 1 μm, the lower electrode 11 has almost no material limitation as long as it has conductivity. Therefore, there is no problem if it is formed using a conductive metal such as an Al-based material or ITO.

  On the other hand, when the semiconductor layer 21 is thin (around 0.2 to 0.5 μm), light is not sufficiently absorbed by the semiconductor layer 21, so that an increase in leakage current due to light irradiation to the TFT switch 4 is prevented. An alloy mainly composed of a light-shielding metal or a laminated film is preferable.

  A semiconductor layer 21 that functions as a photodiode is formed on the lower electrode 11. In the present embodiment, a PIN structure photodiode in which an n + layer, an i layer, and a p + layer (n + amorphous silicon, amorphous silicon, p + amorphous silicon) are stacked is adopted as the semiconductor layer 21, and the n + layer 21A is formed from the lower layer. , I layer 21B and p + layer 21C are sequentially stacked. The i layer 21 </ b> B generates charges (a pair of free electrons and free holes) when irradiated with light. The n + layer 21A and the p + layer 21C function as contact layers, and electrically connect the lower electrode 11 and an upper electrode 22 (described later) and the i layer 21B.

  On each semiconductor layer 21, an upper electrode 22 is formed individually. For the upper electrode 22, for example, a material having high light transmittance such as ITO or IZO (zinc oxide indium) is used. In the radiation detector 10 according to the present exemplary embodiment, the sensor unit 103 includes the upper electrode 22, the semiconductor layer 21, and the lower electrode 11.

  On the interlayer insulating film 12, the semiconductor layer 21, and the upper electrode 22, a coating type interlayer insulating film 23 is formed so as to have a part of the opening 27 </ b> A corresponding to the upper electrode 22 and cover each semiconductor layer 21. Yes.

  On the interlayer insulating film 23, the bias line 25 is formed of Al or Cu, or an alloy or laminated film mainly composed of Al or Cu. The bias line 25 has a contact pad 27 formed in the vicinity of the opening 27 </ b> A and is electrically connected to the upper electrode 22 through the opening 27 </ b> A of the interlayer insulating film 23.

  On the other hand, as shown in FIG. 6, in the radiation detection pixel 20B of the radiation detector 10, the TFT switch 4 is formed so that the source electrode 9 and the drain electrode 13 are in contact with each other. That is, in the pixel 20B, the source and drain of the TFT switch 4 are short-circuited. Thereby, in the pixel 20 </ b> B, the electric charge collected in the lower electrode 11 flows out to the signal wiring 3 regardless of the switching state of the TFT switch 4.

  A scintillator is provided on the surface of the radiation detector 10 thus formed. For example, if necessary, a protective film is formed of an insulating material having a low light absorption property, and a scintillator made of GOS or the like is attached to the surface of the radiation detector 10 using an adhesive resin having a low light absorption property. . Further, for example, a scintillator made of CsI or the like is directly deposited on the surface of the radiation detector 10. CsI may be attached to the surface of the radiation detector 10 using an adhesive resin having low light absorption after being deposited on the support.

  Next, a flow of operations when radiographic images are captured by the radiographic image detector 100 having the above configuration will be described. In the present embodiment, a radiographic image is taken under the control of the control unit 106 based on an instruction from the control device 202. In the control unit 106, when an imaging instruction is received from the control device 202, the following processing is executed by the radiographic imaging program being executed by the CPU. FIG. 7 shows a flowchart of an example of the flow of the entire process. The radiographic image capturing program may be stored in the radiographic image detector 100 in advance, or may be supplied from the outside such as a CD-ROM, USB, or the control device 202.

  When receiving a photographing instruction from the control device 202, the control unit 106 starts driving the amplifier 52 of the amplifier circuit 50 of the signal detection circuit 105 in step 100 and continuously drives it. As a result, the control unit 106 acquires an electrical signal (a value converted into a digital signal, hereinafter simply referred to as an electrical signal) output from the radiation detection pixel 20B to the signal wiring 3.

  In the next step 102, the acquired electric signal is compared with a predetermined first threshold value for detecting the start of radiation irradiation, and detection of whether or not radiation irradiation has started is made based on whether or not the first threshold value is exceeded. Do. Note that the detection of the start of radiation irradiation by the control unit 106 is not limited to whether or not the radiation threshold value is equal to or greater than the first threshold value for radiation detection. You may make it detect. If the electrical signal is less than the first threshold, it is denied that radiation irradiation has not started, and a standby state is entered. On the other hand, if the electrical signal is equal to or greater than the first threshold, it is determined that radiation irradiation has started, and the determination is affirmed and the process proceeds to step 103.

  In step 103, in order to start radiographic imaging, the scanning wiring drive circuit 104 is instructed to output a drive signal that becomes a gate-off signal (a signal for turning off the gate of the TFT switch 4). Thereby, in the sensor unit 103 of the radiographic image capturing pixel 20A, accumulation of electric charges generated in response to radiation irradiation is started. On the other hand, the radiation detection pixel 20 </ b> B outputs charges generated in response to radiation irradiation to the signal wiring 3 regardless of the gate-off signal.

  In the next step 104, the control unit 106 starts acquiring the change with time of the electrical signal output from the radiation detection pixel 20B to the signal wiring 3, and in the next step 106, the control unit 106 determines in advance to acquire the change with time. It is determined whether or not a predetermined time has passed. If the predetermined time has not elapsed, the acquisition of the change with time of the electric signal is continued. On the other hand, if the predetermined time has elapsed, the acquisition of the change with time of the electrical signal is stopped and the routine proceeds to step 108. The predetermined time is determined in advance by an experiment or the like as appropriate for noise detection.

  In step 108, the presence / absence, intensity, and generation period of noise are detected by signal analysis processing.

  Here, before describing the signal analysis processing of the present embodiment, first, noise generated in the radiographic image capturing apparatus 201 (the radiographic image detector 100) will be described. FIG. 8 shows a specific example of the temporal change in intensity of the irradiated radiation (electrical signal generated by the radiation). On the other hand, noise appearing in an electric signal is roughly divided into two types of noise. The waveform of the electric signal due to noise is AC noise (see FIG. 9A) and the shape of the electric signal due to noise is rectangular noise whose waveform is a rectangular wave (see FIG. 9B). The AC noise includes AC noise generated from other electronic devices and the like, and impact noise generated when an impact is applied to the signal wiring 3 and the cable wiring of the radiation detector 10. FIG. 9A shows AC noise having a low intensity and a short generation period. On the other hand, the rectangular noise includes rectangular noise generated due to an increase in dark current due to the pressure (charge generation due to the piezoelectric effect) to the sensor unit 103 of the radiation image detector 100 and the temperature rise of the sensor unit 103. . FIG. 9B shows rectangular noise having a low intensity and a short generation period.

  Hereinafter, as a specific example, a case where generated noise is AC noise will be described in detail, but it goes without saying that the same applies to rectangular noise.

  FIG. 10 shows a flowchart of a specific example of the flow of signal analysis processing of the present embodiment.

  In step 200, differential processing is performed on the time change of the electrical signal. Note that the differentiation process may be a general differentiation process. As a specific example, FIG. 11 shows a profile of the change over time of the strength of the electrical signal before the differentiation process. FIG. 11A shows a change over time in the intensity of an electric signal based only on charges generated by radiation irradiation, which does not include noise. FIG. 11B shows a case where an electric signal caused by the AC noise is added to the electric signal shown in FIG. 11A when AC noise having a high intensity and a short generation period is generated. Indicates. Further, in FIG. 11C, when AC noise having a high intensity and a long generation period is generated, an electric signal caused by the AC noise is added to the electric signal shown in FIG. Indicates.

  As a specific example, FIG. 12 shows a profile of the time change of the strength of the electric signal obtained by differentiating the time change of the electric signal shown in FIG. FIG. 12A corresponds to FIG. FIG. 12B corresponds to FIG. Further, FIG. 12C corresponds to FIG.

  In the present embodiment, a second threshold value for detecting presence / absence of noise and a third threshold value for detecting noise intensity are set in advance. In step 202, it is determined whether or not the intensity of the differentiated electrical signal (hereinafter simply referred to as an electrical signal if it is not necessary to distinguish it from that before differentiation) is equal to or less than a second threshold value. In step 204, it is determined whether or not the intensity of the electric signal is equal to or less than a third threshold value. Note that both the positive and negative values are set for the second threshold and the third threshold, and when the intensity of the differentiated electrical signal reaches both the positive and negative values, Judged that the three thresholds were exceeded. In the present embodiment, the second threshold value <the third threshold value.

  A specific example of noise determination in the signal analysis of the present embodiment is shown in FIG. In the present embodiment, when the intensity of the electric signal is equal to or lower than the second threshold, it is detected that no noise is generated. On the other hand, when the intensity of the electric signal exceeds the second threshold, it is detected that noise has occurred. Further, when the occurrence of noise is detected (the electric signal intensity exceeds the second threshold value), if it is equal to or less than the third threshold value, it is detected that the intensity of the generated noise is weak. On the other hand, when the third threshold value is exceeded, it is detected that the intensity of the generated noise is strong.

  In the signal analysis of the present embodiment, the noise generation period is detected based on the number of times that the intensity of the electric signal exceeds the third threshold within a predetermined unit time. In the present embodiment, when the number of times that the intensity of the electric signal exceeds the third threshold is less than n, it is detected that the noise generation period is short. On the other hand, when the number of times that the intensity of the electric signal exceeds the third threshold is n times or more, it is detected that the noise generation period is long. The unit time and “n” described above may be obtained in advance through experiments or the like. In the present embodiment, the length of the noise generation period is detected based on the number of times the third threshold is exceeded. However, the present invention is not limited to this. For example, the noise generation period may be detected based on the number of times the second threshold is exceeded. .

  If the electric signal is equal to or smaller than the second threshold value in step 202 described above, it is detected that noise has not occurred, and the process is terminated. On the other hand, if the electrical signal exceeds the second threshold value, it is determined that noise has occurred, so the result is negative and the process proceeds to step 204. In step 204, if the electrical signal is equal to or smaller than the third threshold value, the determination is affirmative and the process proceeds to step 206, where it is detected that the noise intensity is weak and weak noise, and the signal analysis process is terminated. On the other hand, if the electrical signal exceeds the third threshold value, the result is negative and the process proceeds to step 208. After detecting that the noise is strong and strong, the process proceeds to step 210.

  In step 210, it is determined whether or not the number of times that the electric signal has reached or exceeded the third threshold is n or more. If it is n times or more, the determination is affirmed and the routine proceeds to step 212, where it is detected that the noise generation period is long, and the signal analysis processing is terminated. On the other hand, if it is less than n times, the determination is negative and the process proceeds to step 214, where it is detected that the noise generation period is short and the signal analysis process is terminated.

  Thus, when the signal analysis processing (FIG. 7, step 108) is completed, the control unit 106 of the radiation image detector 100 proceeds to step 110. In step 110, it is determined whether or not to display a radiographic image based on the result of the signal analysis process. In the present embodiment, the captured radiographic image is output from the control unit 106 to the control device 202 and displayed on the display unit 212 of the control device 202. For this reason, in this embodiment, when it is determined that the radiographic image is not displayed, the radiographic image is not output from the control unit 106 to the control device 202.

  In the present embodiment, the occurrence of noise is detected, and when it is detected that the intensity of the generated noise is strong and the generation period is long, the radiation image is not displayed. Therefore, if it is detected by the signal analysis process that the intensity of the generated noise is strong and the generation period is long, the determination is negative and the process proceeds to step 112. In step 112, the notification unit 108 notifies the user who takes a radiographic image that noise having a high intensity and a long generation period has occurred. As a specific example, in the present embodiment, when the notification unit 108 is configured by an LED (see FIG. 3A), it blinks at intervals of 0.2 seconds to notify the user. Give a strong warning. Further, when the notification unit 108 is configured by an LED and a speaker, the LED is blinked at intervals of 0.1 seconds, and a warning sound is generated by the speaker to notify the user so as to give a strong warning. It may be. The notification method is not limited to this, and is not particularly limited as long as it can be distinguished from weak noise and noise with a short generation period, which will be described later. Further, instead of the notification unit 108 of the radiation image detector 100, the display unit 212, the notification unit 213, or the like of the control device 202 may be used, or both the radiation image detector 100 and the control device 202 may be used. Good. Further, in the present embodiment, in the case of noise having a high intensity and a long generation period, a radiographic image is not displayed (output), so that the fact is displayed on the display unit 212 of the control device 202 and re-imaging is performed. It is good to display a prompt to the user.

  By notifying as described above, the user can recognize the occurrence of noise having a strong intensity and a long generation period, and therefore can stop radiographic image capturing and appropriately perform re-imaging. As a specific example, after the subject 206 is unpositioned, the noise source is confirmed and removed, the subject 206 is positioned again, and the control device 202 is instructed to take a radiographic image. In addition, since the user can recognize the occurrence of noise by the above notification, re-imaging can be performed without feeling uncomfortable that the radiation image is not displayed.

  In addition, when noise with such a strong intensity and a long generation period is generated, the radiation irradiation device 204 may be instructed to stop the radiation irradiation via the control device 202. By doing so, the exposure dose of the subject 206 can be reduced.

  In step 114 after notifying the user, the control unit 106 instructs to output a drive signal that becomes a gate-on signal (a signal for turning on the gate of the TFT switch 4), and the radiographic imaging pixel. After resetting the electric charge accumulated in the sensor unit 103 of 20A, this process is terminated. In this embodiment, since the generation of the radiographic image itself is not performed, the charge accumulated in the radiographic image capturing pixel 20A is reset in this way to prepare for re-imaging. Here, in order to output a gate-on signal to reset the charge accumulated in the radiographic image capturing pixel 20A, an on signal is simultaneously output to all the radiographic image capturing pixels 20A (scanning wiring 101). What should I do? Further, after resetting the charge accumulated in the sensor unit 103 of the radiographic image capturing pixel 20A, the amplifier 52 in step 100 may be returned to the continuously driven state.

  On the other hand, when noise is not generated, and when noise is generated and at least one of noise that is weak in intensity and noise that has a short generation period, a radiation image is displayed (captured). If the result is affirmative, the routine proceeds to step 116. In step 116, it is determined whether noise has occurred. If no noise has been generated, the determination is negative and the routine proceeds to step 120. On the other hand, if at least one of weak noise and noise having a short generation period has occurred, the determination is affirmative and the process proceeds to step 118, and at least one of noise having a low intensity and noise having a short generation period has occurred. Is notified to the user who takes a radiographic image. As a specific example, in the present embodiment, when the notification unit 108 is configured by an LED (see FIG. 3A), it blinks at intervals of 0.5 seconds to notify the user. Give a warning. Further, when the notification unit 108 is configured by an LED and a speaker, a warning may be given by generating a warning sound at intervals of 0.5 seconds from the speaker and notifying the user. The notification method is not limited to this, and is not particularly limited as long as it can be distinguished from the above-described noise having a high intensity and a long generation period. Similarly to the above, instead of the notification unit 108 of the radiation image detector 100, the display unit 212 and the notification unit 213 of the control device 202 may be used, or both the radiation image detector 100 and the control device 202 may be used. You may make it use.

  In this way, the notification allows the user to recognize that at least one of low-intensity noise and noise with a short generation period has occurred before the radiographic image is displayed, so the radiographic image is an abnormal image. It is possible to prepare for re-photographing to be performed in some cases. As a specific example, it is possible to instruct the subject 206 not to move the body without changing the position of the subject 206 even after taking the radiographic image, and to immediately re-photograph after confirming the displayed radiographic image. . Note that when the confirmation is made, the degree of abnormality appearing in the radiographic image is low. For example, in the case of image unevenness of longitude that is outside a desired range, re-imaging may not be performed.

  In the next step 120, it is determined whether or not a predetermined charge accumulation time has elapsed for radiographic imaging. If it has not elapsed, it is denied and enters a standby state. On the other hand, if it has elapsed, the determination is affirmed and the routine proceeds to step 122. In step 122, since it is necessary to acquire an electrical signal for each pixel 20 (radiation image capturing pixel 20 </ b> A), the control unit 106 performs driving that becomes a gate-on signal (a signal for turning on the gate of the TFT switch 4). An instruction is given to sequentially output the signals for each scanning wiring 101, and an electric signal corresponding to the charge accumulated in the sensor unit 103 of the radiographic image capturing pixel 20A is acquired. Further, the control unit 106 generates a radiation image based on the acquired electrical signal. In the next step 124, the generated radiation image is output and output to the control device 202 so as to be displayed, and then this process is terminated.

  As described above, in the radiographic image capturing apparatus 201 of this embodiment, when radiographic image capturing is instructed, the control unit 106 of the radiographic image detector 100 converts the charge output from the radiation detection pixel 20B. The corresponding electrical signal is compared with the first threshold value, and when the first threshold value is exceeded, it is detected that radiation irradiation has started. When radiation irradiation is started, the control unit 106 controls the sensor unit 103 of the radiographic image capturing pixel 20A to accumulate electric charge, and generates an electric signal corresponding to the electric charge output from the radiation detection pixel 20B. Obtain changes over time. Furthermore, the control unit 106 performs a differentiation process on the acquired electrical signal with time by signal analysis, and detects that noise has occurred when the second threshold is exceeded. Furthermore, when the third threshold value is exceeded, it is detected that the intensity of the generated noise is strong. Furthermore, when the number of times the third threshold is exceeded is n or more, it is detected that the noise generation period is long. When the intensity of the generated noise is strong and the generation period is long, the notification unit 108 notifies the user and does not generate and display (output) the radiation image. On the other hand, when at least one of weak noise and noise having a short generation period is notified to the user by the notification unit 108, a radiographic image is generated and displayed on the display unit 212 of the control device 202.

  Therefore, the radiographic image capturing apparatus 201 of the present embodiment can appropriately detect and notify the presence or absence of noise when capturing a radiographic image.

  Here, as a comparative example, a radiographic imaging apparatus that does not perform signal analysis processing of the acquired electrical signal performed by the control unit 106 described above, that is, does not detect the presence or absence of noise, and does not include the notification unit 108. A radiographic image was taken. In this case, unlike the above-described embodiment, the user cannot recognize that noise has occurred during radiographic imaging until the radiographic image is displayed. I had to start over and re-shoot. Further, as a comparative example, a radiographic image is captured by a radiographic imaging device that performs signal analysis processing of the acquired electrical signal performed by the control unit 106 described above (detects the presence or absence of noise) but does not include the notification unit 108. went. In this case, if the intensity of the generated noise is strong and the generation period is long, the radiographic image is not displayed and the user may mistake the radiographic imaging device for failure. Problems such as shooting. If the noise is at least one of weak noise and short generation noise, the user cannot recognize that the noise has occurred until the radiographic image is displayed. I had to re-shoot from positioning.

  On the other hand, in the present embodiment, as described above, the presence / absence of noise can be appropriately detected and notified at the time of radiographic image capture, so that the burden on the user can be reduced. Further, when re-photographing is performed, re-photographing can be performed promptly. Furthermore, since it is possible to recognize whether or not an abnormality has occurred in the radiographic image due to noise, the possibility of misdiagnosis can be suppressed.

[Second Embodiment]
Next, a second embodiment will be described.

  Since the pixel 20 and the radiation image detector 100 of the present embodiment have substantially the same configuration and operation as those of the first embodiment, description of the same parts will be omitted. In the radiological image detector 100 of the present embodiment, only part of the above-described signal analysis processing (see FIG. 10) is different, so only different processing will be described here.

  FIG. 14 shows a flowchart of an example of the signal analysis process of the present embodiment. In this embodiment, instead of the differentiation process performed in the first embodiment, the difference of the moving average of the time change of the electric signal is used. Therefore, in step 300, the moving signal is time-averaged over time. In the next step 301, the moving average is subtracted from the current electrical signal to calculate the difference. As a specific example, FIG. 15 shows a time change profile of the difference of the moving average difference of the electric signal change with time shown in FIG. FIG. 15A corresponds to FIG. FIG. 15B corresponds to FIG. Further, FIG. 15C corresponds to FIG.

  The next step 302 corresponds to step 202 (see FIG. 10) of the signal analysis processing of the first embodiment, and compares the difference with the second threshold value. The next step 304 corresponds to step 204 (see FIG. 10) of the signal analysis processing of the first embodiment, and compares the difference with the third threshold value. Hereinafter, step 306 to step 314 of the signal analysis processing of the present embodiment correspond to step 206 to step 214 of the signal analysis processing of the first embodiment, and the same processing is performed.

  As described above, in the present embodiment, since the presence / absence, intensity, and generation period of noise are detected using the difference of the moving average of the time change of the electrical signal, the present embodiment is similar to the first embodiment. The radiographic image capturing apparatus 201 of the embodiment can appropriately detect and notify the presence or absence of noise when capturing a radiographic image.

[Third Embodiment]
Next, a third embodiment will be described. In the present embodiment, description of substantially the same configuration and operation as those of the first embodiment will be omitted. In the first embodiment, the control unit 106 collectively acquires the electrical signals output from the radiation detection pixels 20B to the signal wirings 3 as one electrical signal. The radiation image detector 100 is configured to acquire an electrical signal output for each signal wiring 3 (each amplifier circuit 50), and detect and notify the presence or absence of noise for each acquired electrical signal. Yes.

FIG. 16 is a configuration diagram showing an example of the overall configuration of the radiation image detector 100 of the present embodiment. In the present embodiment, an example of the radiation image detector 100 when the radiation detection pixel 20B is provided for each signal wiring 3 is shown. Further, in order to distinguish the electric signal output for each signal wiring 3 (D1 to D4), when distinguishing the amplification circuit 50 and the like of the signal detection circuit 105 connected to each, as shown in FIG. Like the amplifier circuits 50 ₁ to 50 ₄ , numbers for distinguishing the individual circuits are attached, and the collective names are simply referred to as the amplifier circuits 50.

  FIG. 17 shows a flowchart of an example of the flow of the entire radiographic image capturing process in the radiographic image detector 100 of the present embodiment. Since this process includes substantially the same steps (processes) as the entire imaging process (FIG. 7) in the radiation image detector 100 according to the first embodiment, The detailed description is omitted.

  Steps 400 to 403 of the shooting process of the present embodiment correspond to steps 100 to 103 (see FIG. 7) of the shooting process of the first embodiment, respectively. When an instruction to capture a radiographic image is given, driving of the amplifier 52 of the amplifier circuit 50 is started. When the acquired electrical signal is equal to or higher than the first threshold, it is determined that radiation irradiation has started, and the scanning wiring driving circuit A gate-off signal is output to 104 to cause the radiographic image capturing pixel 20A to start accumulating charges.

The next step 404 corresponds to step 104 of the imaging process of the first embodiment, and changes in the electrical signal output from the radiation detection pixel 20B to each signal wiring 3 (amplifier circuit 50) over time. Start acquisition. In the form of a specific embodiment, to obtain an electric signal outputted to the signal lines 3 (D1) from the amplifier circuit 50 _1. Similarly, to get the electric signal outputted to the signal lines 3 (D2) from the amplification circuit 50 _2, acquires the electric signal outputted to the signal lines 3 (D3) from the amplifier circuit 50 _3, the signal lines 3 (D4 the electric signal output in) obtained from the amplifying circuit 50 _4.

  The next step 406 corresponds to step 106 of the photographing process of the first embodiment, and determines whether or not a predetermined time has passed. If not, the electric signal of each signal wiring 3 is determined. Continue to acquire changes over time. On the other hand, if the predetermined time has elapsed, the acquisition of the change with time of the electrical signal is stopped and the routine proceeds to step 408.

  Step 408 corresponds to Step 108 of the imaging process of the first embodiment, and the presence or absence of noise, intensity, and the like for each signal wiring 3 (area corresponding to the signal wiring 3) by signal analysis processing. Detect the occurrence period. FIG. 18 shows a flowchart of a specific example of the flow of signal analysis processing of the present embodiment. Note that this signal analysis processing corresponds to the signal analysis processing (see FIG. 10) of the first embodiment, and shows a case where differentiation processing is performed with respect to a time change of the electrical signal. As in the signal analysis process (see FIG. 14) of the embodiment, the difference of the moving average of the time change of the electrical signal may be used.

  Step 500 to step 514 of the signal analysis processing according to the present embodiment is the signal analysis processing according to the first embodiment except that the time change of the electric signal is differentiated for each signal wiring 3 in step 500. The processing corresponding to each of Step 200 to Step 214 is performed. When the time change of the electrical signal of one signal wiring 3 is differentiated and the intensity of the differentiated electrical signal (hereinafter simply referred to as an electrical signal) is less than or equal to the second threshold, it is determined that no noise has occurred. Proceed to step 515. On the other hand, if the second threshold value is exceeded, noise has occurred, so the intensity of the electrical signal is compared with the third threshold value. If the second threshold value is less than the third threshold value, the noise is determined to be weak and the process proceeds to step 515. . On the other hand, if the third threshold value is exceeded, strong noise is determined, and if it occurs more than n times, it is determined that the generation period is long, and if it is less than n times, the generation period is determined to be short and the process proceeds to step 515. move on.

  In step 515, the presence / absence of noise, the strength, and the length of the generation period are stored for each signal wiring 3. In the present embodiment, the presence / absence, strength, and occurrence period of detected noise are determined for each region corresponding to each signal wiring 3 (region determined by the pixel 20 that outputs an electric signal to the signal wiring 3). Remember long and short.

  In the next step 516, it is determined whether or not the detection and storage of the presence / absence of noise, the strength, and the length of the generation period have been detected and stored for all the signal wirings 3. If not, the result is negative and the process returns to step 500 to repeat the signal analysis process. On the other hand, when the processing is finished, the determination is affirmed and the signal analysis processing is finished.

  When the signal analysis process is completed in this way, the control unit 106 of the radiation image detector 100 proceeds to Step 410. In step 410 of the imaging process of the present embodiment, it is determined based on the processing result of the signal analysis process described above whether or not there is a region where noise is generated with a high intensity and a long generation period. If there is no region where noise is generated with a high intensity and a long generation period, the determination is negative and it is determined that a radiographic image is to be displayed, and the process proceeds to step 416. On the other hand, if there is a region where noise is generated with a high intensity and a long generation period, the determination is affirmed and the process proceeds to step 411.

  In step 411, it is determined whether the number of generated areas is equal to or greater than a fourth threshold value. In the first embodiment and the second embodiment, when the intensity of the detected noise is strong and the generation period is long, control is performed so as not to display the radiation image. Even when the intensity of noise is high and the generation period is long, if the number of generated areas is small, control is performed so that a radiation image is displayed. Therefore, in the radiation image detector 100 of the present embodiment, a fourth threshold value for determining whether to display an image is determined in advance. Note that the fourth threshold value may be determined based on the number of regions where noise is difficult to visually recognize, the number of regions where trouble is difficult to visually recognize, etc. in advance, or set by the user. You may make it do.

  If it is determined in step 411 that the number of regions is less than the fourth threshold value, the determination is negative and a radiographic image is displayed, and the process proceeds to step 416. On the other hand, if the number of areas is equal to or greater than the fourth threshold, the determination is affirmed and no radiographic image is displayed, and the process proceeds to step 412.

Step 412 corresponds to step 112 of the imaging process of the first embodiment, and the notification unit 108 notifies the user that noise having a high intensity and a long generation period has been detected. The method of notifying the user may be notified in the same manner as in the first embodiment, but it is preferable to notify the user so as to indicate the area where the noise is detected. In the radiation image detector 100 of the present embodiment, a notification unit 108 is provided so that notification can be made so as to indicate a region where noise is detected. FIG. 19 shows an example of the appearance of the radiation image detector 100 (housing 120) of the present embodiment. FIG. 19A shows a case where the notification unit 108 is an LED, and corresponds to FIG. 3A of the first embodiment. FIG. 19B shows a case where the notification unit 108 is a speaker, and corresponds to FIG. 3B of the first embodiment. As shown in FIG. 19, in the present embodiment, a notification unit 108 is provided at a position corresponding to each region, and the notification unit 108 corresponding to the position of the region where noise is detected is used. In the same manner as in the embodiment, the user is notified of the detected noise. In the radiation image detector 100 (housing 120) shown in FIG. 19, the notification unit 108 ₁ corresponds to the region corresponding to the signal lines 3 (D1), the notification unit 108 ₂ corresponding to the signal lines 3 (D2) corresponds to the region, corresponding to the area where the notification unit 108 ₃ corresponding to the signal lines 3 (D3), respectively correspond to the area where the notification unit 108 ₄ corresponding to the signal lines 3 (D41). For example, when it is detected that the electrical signal output to the signal wiring 3 (D1) and the electrical signal output to the signal wiring 3 (D2) have a strong intensity and a long generation period, noise is generated. 108 ₁ and the notification unit 108 ₂ notify that noise having a high intensity and a long generation period is detected.

  The next step 414 corresponds to step 114 of the imaging process of the first embodiment, and the control unit 106 instructs to output a drive signal that becomes a gate-on signal, and the radiographic image capturing pixel 20A. After resetting the electric charge accumulated in, this processing is terminated.

  On the other hand, Steps 416 to 424 when it is determined to display a radiation image correspond to Steps 116 to 124 of the imaging processing according to the first embodiment, respectively. It is determined whether or not there is a region where noise is detected. If there is a region where noise is detected, the detection of the noise and the detected region are notified. In the present embodiment, notification according to the type (intensity and length) of the detected noise is performed in the same manner as in the first embodiment. Further, in the same manner as in step 412 described above, a notification is given to indicate the detected area.

  When the charge accumulation time for radiographic image capture has elapsed, an instruction is given to sequentially output a drive signal serving as a gate-on signal for each scanning wiring 101, and the electric power corresponding to the electric charge accumulated in the radiographic image capture pixel 20A. A signal is acquired, and a radiation image is generated based on the acquired electrical signal. In step 424 of the present embodiment, the generated radiation image is output to the control apparatus 202, and information indicating the area where the noise is detected (alarm area for warning the user) is output to the control apparatus 202. Furthermore, after outputting to the control apparatus 202 so that the information regarding a radiographic image and an alarm area | region may be displayed, this process is complete | finished.

  In the control device 202 of the present embodiment, the radiographic image is displayed based on the display instruction of the information regarding the radiographic image and the alarm area output from the radiographic image detector 100 in this way. FIG. 20 shows a flowchart of an example of an image display process of a radiographic image executed by the control device 202 of the present embodiment. In this embodiment, when radiographic image capturing is instructed, the control unit 210 of the control device 202 executes this process.

In step 600, it is determined whether or not a radiation image (electrical signal indicating a radiation image) has been input. If it has not been entered yet, it will be denied and will enter a standby state. On the other hand, if a radiographic image is input in step 424 of the imaging process described above, the determination is affirmed and the process proceeds to step 602. In step 602, the input radiation image is displayed on the display unit 212. A specific example of the radiation image display in the present embodiment is shown in FIG. As shown in FIG. 21, in the present embodiment, the display unit 212 has a radiation image 60, an alarm region display unit 62 (62 _{1 to} 62 ₄ ) indicating an alarm region, and a radiation image in which a user is displayed. An instruction unit 64 and an instruction unit 66 for instructing execution of image processing are displayed.

The radiation image 60 corresponds to the radiation image input from the radiation image detector 100. FIG. 21 shows a case where a radiation image 60 including noise N is displayed. The alarm area display unit 62 is not particularly limited as long as it can display the position of the input alarm area so that the user can recognize it. In the present embodiment, as a specific example, as shown in FIG. 21, alarm area display units 62 ₁ to 62 ₄ are provided corresponding to the respective areas, and the alarm areas are turned on or blinking. It is configured as follows. In Figure 21, in that it detects generate noise (see Noise N) of the region corresponding to the signal lines 3 (D2) has a alarm region, shows a case where light the alarm region display section 62 _2.

  The instruction unit 64 is used when the user instructs the image processing for removing the noise N to the displayed radiation image 60 (details will be described later). The instruction unit 66 is used when the user instructs to end the display of the radiation image 60.

  When the radiation image 60 is displayed, in the next step 604, it is determined whether or not there is an alarm area. If not, the determination is negative and the process proceeds to step 614. On the other hand, if there is an alarm area, the determination is affirmed and the process proceeds to step 606. In step 606, the alarm area is displayed by the alarm area display unit 62 (see FIG. 21).

  In the next step 608, it is determined whether or not to execute image processing for removing the noise N. If the user has not instructed execution of image processing via the instruction unit 64, the result is negative and the process proceeds to step 614. On the other hand, if the execution of image processing is instructed, the determination is affirmative and the routine proceeds to step 610. In step 610, image processing for removing noise N is performed on the radiation image 60 (image information corresponding to the radiation image 60). Note that the image processing is not particularly limited, and an appropriate filter process or the like for removing the noise N may be determined in advance through experiments or the like. In the next step 612, the radiation image 60 after image processing is displayed on the display unit 212.

  In the next step 614, it is determined whether or not to end the display of the radiation image 60. If the user has not instructed the end through the instructing unit 66, the determination is negative, the process proceeds to step 608, and this process is repeated. On the other hand, if the end is instructed, the determination is affirmative and the routine proceeds to step 616. In step 616, the radiographic image 60 (image information corresponding to the radiographic image 60) and information related to the alarm region are stored in association with each other, and then the present process is terminated. Note that the radiation image 60 to be stored may be the one before image processing in step 610 or the one after image processing. The storage location may be a storage unit such as a memory (not shown) in the control device 202, or a storage unit outside the control device 202 (radiation image capturing apparatus 201).

  Thus, in the present embodiment, the control unit 106 acquires the electrical signal output for each signal wiring 3 (each amplification circuit 50), and the presence / absence of noise, intensity, and Since the length of the generation period is detected, the user can recognize the position (region) where the noise is detected. Moreover, in this Embodiment, the radiographic image 60 is displayed according to the number of the area | regions which detected noise, and when there are few areas, the radiographic image 60 is displayed. When the number of detected regions is small, the display of the radiation image 60 can be prioritized over the re-imaging and the user can confirm the radiation image 60, so that the re-imaging load can be reduced.

[Fourth Embodiment]
Next, a fourth embodiment will be described. Since the present embodiment has substantially the same configuration and operation as the third embodiment, the description of the same parts will be omitted. In the third embodiment, when the number of areas (alarm areas) in which noise is detected is small, the radiographic image 60 is controlled to be displayed. However, in the radiographic image detector 100 according to the present embodiment, The radiographic image 60 is controlled to be displayed in accordance with the position of the alarm area.

  FIG. 22 is a flowchart illustrating an example of the flow of the entire radiographic image capturing process in the radiographic image detector 100 according to the present embodiment. Since this process includes substantially the same steps (processes) as the entire imaging process (FIG. 17) in the radiation image detector 100 of the third embodiment, The detailed description is omitted.

  Steps 700 to 724 of the shooting process of the present embodiment correspond to steps 400 to 424 (see FIG. 17) of the shooting process of the third embodiment, respectively. In the present embodiment, since the processing in step 711 is different from step 411 in the imaging processing in the third embodiment, the processing will be described in detail.

  In step 711 when it is determined in step 710 that there is a region where noise is detected with a strong intensity and a long generation period, it is determined whether or not the position of the region where noise is detected is the center of the radiation image 60. In the present embodiment, the center of the radiographic image 60 is determined in advance by an area corresponding to the radiographic image 60 or an area set by the user. In general, an important image such as a region of interest that the user wants to observe is displayed near the center of the radiation image 60. On the other hand, there are few cases where an important image is displayed around the radiation image 60, and there is often no problem even if noise is generated in the surrounding area. For this reason, in the present embodiment, the center of the radiation image 60 on which such an important image is displayed is obtained in advance by experiments or the like, or set by the user. When noise having a strong intensity and a long generation period is detected at the center of the radiation image 60, control is performed so that the radiation image 60 is not displayed. On the other hand, even if the noise is strong and has a long generation period, if it occurs in the vicinity (area excluding the center), it notifies the user that the noise has been detected and warns the user. Control to display.

  In addition, when the user sets the center of the radiation image 60 described above, for example, an instruction unit is provided corresponding to each alarm region together with the alarm region display unit 62 illustrated in FIG. It may be configured such that the user can indicate a good position or a position where noise should not occur. In the present embodiment, the “center” is used for convenience of explanation, but the user sets the entire region of the radiographic image 60 (specifically, the entire alarm region), and places it at the position of the region where noise is generated. Needless to say, the radiation image 60 can be set to be displayed. When the display of the radiation image 60 is urgently required, such as for emergency use, it is preferable to prioritize the display of the radiation image 60 regardless of the type or position of noise.

  If it is determined in step 711 that the position of the area where the noise is generated is in the center of the radiation image 60, the process proceeds to step 712, and the processing after step 712 is performed in which it is determined that the radiation image 60 is not displayed. On the other hand, if it is determined that it is not the center, the process proceeds to step 716, and the processing after step 716 in which it is determined to display the radiation image 60 is performed. When the radiographic image 60 is displayed, the radiographic image 60 is controlled by the control device 202 so that the user can recognize the detected noise type (strength and length) and the alarm area, as in the third embodiment. After instructing display on the display unit 212, the present process is terminated.

  As described above, in the present embodiment, when the control unit 106 detects noise having a high intensity and a long generation period, the control unit 106 performs control so that the radiation image 60 is displayed according to the position of the area where the noise is detected. When the area where noise is detected is not an area where an important image is displayed, priority can be given to the display of the radiation image 60. Further, the user can recognize the position (region) where the noise is detected. Furthermore, in the present embodiment, display of the radiation image 60 can be prioritized regardless of noise detection.

  Note that the combination of the third embodiment and the fourth embodiment controls whether or not to display the radiation image 60 according to the number and position of the areas where noise is generated with a high intensity and a long generation period. You may make it do. Similarly to the third embodiment and the fourth embodiment, even when the detected noise intensity is weak or the generation period is short, the radiation depends on the number and position of the regions. You may make it control whether the image 60 is displayed.

  In the third embodiment and the fourth embodiment, the change over time of the electrical signal is acquired for each signal wiring 3 (amplifier circuit 50). However, the present invention is not limited to this. ) For each signal wiring 3 (amplifier circuit 50), the above-described control processing may be performed on the region corresponding to the plurality of signal wirings 3.

  In the radiation image detector 100 of the third embodiment and the fourth embodiment, the radiation detection pixels 20B are provided for each signal wiring 3 as shown in FIG. Even when the radiation detection pixels 20B are provided in some of the signal wirings 3 as in the radiation image detector 100 (see FIG. 2) of the first embodiment, the radiation detection pixels 20B The above-described control process may be performed for each signal wiring 3 provided.

[Fifth Embodiment]
Next, a fifth embodiment will be described. In the present embodiment, the description of the configuration and operation substantially the same as those of the above-described embodiment will be omitted. In the radiation image detector 100 of the present embodiment, since the detection method of the start of radiation irradiation is different from the above-described embodiment, the detection method of the start of radiation irradiation will be described.

In the radiation image detector 100 of the present embodiment, the charge flowing through the bias line 25 is detected by the detector 70, and the start of radiation irradiation is detected by the control unit 106 based on the detected charge and the threshold value. FIG. 23 is a configuration diagram showing an example of the overall configuration of the radiation image detector 100 of the present embodiment. FIG. 24 is a configuration diagram showing another example of the overall configuration of the radiation image detector 100 of the present embodiment. In the radiation image detector 100 shown in FIG. 23, the detector 70 is connected to the bias line 25A among the bias lines 25, and the charge flowing through the bias line 25A is detected by the detector 70, and the control unit 106 detects it. The start of radiation irradiation is detected based on the generated charge and the threshold value. On the other hand, in the radiation image detector 100 shown in FIG. 24, a detector 70 (70 ₁ to 70 ₄ ) is provided for each bias line 25, and charges flowing through the bias lines 25 are detected by each detector 70. Then, the start of radiation irradiation is detected based on the charge and threshold value detected by the control unit 106. Note that, as in the radiation image detector 100 shown in FIG. 24, it is preferable to provide a detector 70 for each bias line 25 because determination can be performed according to each region and detection accuracy is improved. .

  A method for detecting the start of radiation irradiation according to the present embodiment will be described. In the present embodiment, substantially the same processing is performed except for the processing of Step 100 and Step 102 (see FIG. 7) for detecting the start of radiation irradiation in the imaging processing of the first embodiment. Description is omitted.

  FIG. 25 shows a flowchart of an example of the irradiation start detection process of the present embodiment.

  In step 800, the scanning wiring drive circuit 104 is instructed to output gate-off signals to all scanning wirings 101. As a result, a gate-off signal is output from the scanning wiring driving circuit 104 to each pixel 20, and the TFT switches 4 of all the pixels 20 are turned off.

  In the next step 802, an electric signal (charge) flowing through the bias line 25 is detected by the detector 70, and in the next step 804, it is determined whether or not the detected electric signal is greater than or equal to a fifth threshold value. The fifth threshold value may be obtained in advance as a threshold value for starting radiation irradiation through experiments or the like. Further, when the radiation image detector 100 is provided with a detector 70 for each bias line 25 as shown in FIG. 24, the electrical signals detected by a predetermined number or more of the detectors 70 become the fifth threshold value or more. It may be determined whether or not the electrical signals detected by all the detectors 70 are equal to or greater than a fifth threshold value. It may be determined in advance according to use of radiographic image detector 100 and photographing, and is not particularly limited.

  If the electrical signal is less than the fifth threshold, the result is negative and the process proceeds to step 806. In step 806, it is determined whether or not a predetermined time for charge reset has elapsed. In the case of the present embodiment, the TFT switch 4 is turned off by the gate-off signal, so that charges are accumulated in all the pixels 20. Unless the accumulated charge is reset, an increase in electrical signals due to noise and a dynamic range are reduced, and the image quality of the radiation image is degraded. For this reason, in the present embodiment, control is performed so that the charge accumulated in the pixel 20 is reset every predetermined time. The predetermined time may be obtained in advance by an experiment or the like according to the radiation image detector 100 or the pixel 20.

  If the predetermined time has not elapsed, the result is negative and the process returns to step 802 to repeat this process. On the other hand, if the predetermined time has elapsed, the determination is affirmed and the process proceeds to step 808. In step 808, the detection operation of the start of radiation irradiation by the detector 70 is temporarily interrupted, and the scanning wiring driving circuit 104 is instructed to output gate-on signals to all the scanning wirings 101. In response to the instruction, driving is performed to reset the charges accumulated in all the pixels 20. After the charge is reset, the process returns to step 800, and the detection operation of the start of radiation irradiation is started again.

  On the other hand, if the electrical signal is greater than or equal to the fifth threshold value in step 804, the determination is affirmative and the process proceeds to step 810, where the start of radiation irradiation is detected, and this process ends.

  As described above, in this embodiment, in a state where the gate-off signal is output to the scanning wiring 101, the charge (electric signal) flowing through the bias line 25 is detected by the detector 70, and the electric signal is compared with the fifth threshold value. When it is equal to or greater than the fifth threshold, the start of radiation irradiation is detected. Thereby, noise (for example, feedthrough noise) due to the output of the gate-on signal to the scanning wiring 101 (ON operation of the TFT switch 4) does not occur, so that the S / N ratio can be improved.

[Sixth Embodiment]
Next, a sixth embodiment will be described. In the present embodiment, the description of the configuration and operation substantially the same as those of the above-described embodiment will be omitted. In the radiation image detector 100 of the present embodiment, since the detection method of the start of radiation irradiation is different from the above-described embodiment, the detection method of the start of radiation irradiation will be described.

  In the radiation image detector 100 of the present embodiment, the control unit 106 detects the start of radiation irradiation based on the current (charge) leaking from the pixel 20 and the threshold value. A configuration diagram showing an example of the overall configuration of the radiation image detector 100 of the present embodiment is shown in FIG.

  A method for detecting the start of radiation irradiation according to the present embodiment will be described. In the present embodiment, substantially the same processing is performed except for the processing of Step 100 and Step 102 (see FIG. 7) for detecting the start of radiation irradiation in the imaging processing of the first embodiment. Description is omitted.

  FIG. 27 shows a flowchart of an example of the irradiation start detection process of the present embodiment.

  In step 900, the scanning wiring drive circuit 104 is instructed to output gate-off signals to all the scanning wirings 101, as in the radiation irradiation start detection process of the fifth embodiment. In response to this instruction, a gate-off signal is output from the scanning wiring driving circuit 104 to each pixel 20, and the TFT switches 4 of all the pixels 20 are turned off.

  In the next step 902, driving of the amplifier circuit 50 (amplifier 52) of the signal detection circuit 105 is started and continuously driven. Even when the TFT switch 4 of the pixel 20 is in an OFF state, a leakage current is generated in response to radiation irradiation, and a charge (electrical signal) corresponding to the leakage current flows through each signal wiring 3. Sampled by (amplifier 52). In the next step 904, the control unit 106 compares the electric signal corresponding to the electric charge sampled by the amplifier circuit 50 with the sixth threshold value or more, and whether or not radiation irradiation is started depending on whether or not the sixth threshold value is exceeded. Detect whether or not. The sixth threshold value may be obtained in advance as a threshold value for starting radiation irradiation through experiments or the like.

  If the electrical signal is less than the sixth threshold, the determination is negative and the process proceeds to step 906. In step 906, it is determined whether or not a predetermined time for charge reset has elapsed. In the present embodiment, as in the fifth embodiment, the TFT switch 4 is turned off by the gate-off signal, so that charges are accumulated in all the pixels 20. Therefore, unless the accumulated electric charges are reset, the image quality of the radiographic image is deteriorated due to an increase in electrical signals due to noise and a decrease in dynamic range. For this reason, in the present embodiment, control is performed so that the charge accumulated in the pixel 20 is reset every predetermined time. The predetermined time (generally different from the “predetermined time” in the fifth embodiment) may be obtained in advance by experiments or the like according to the radiation image detector 100 and the pixels 20.

  If the predetermined time has not elapsed, the result is negative and the process returns to step 904 to repeat the process. On the other hand, if the predetermined time has elapsed, affirmative determination is made and the routine proceeds to step 908. In step 908, the detection operation of the start of radiation irradiation by the detector 70 is temporarily interrupted, and the scanning wiring drive circuit 104 is instructed to output gate-on signals to all the scanning wirings 101. In response to the instruction, driving is performed to reset the charges accumulated in all the pixels 20. After resetting the charge, the process returns to step 900, and the detection operation of the start of radiation irradiation is started again.

  On the other hand, if the electrical signal is greater than or equal to the sixth threshold value in step 904, the determination is affirmative and the process proceeds to step 910, where the start of radiation irradiation is detected, and this process ends.

  As described above, in the present embodiment, in the state where the gate-off signal is output to the scanning wiring 101, the electric signal corresponding to the leakage current flowing from each pixel 20 to the signal wiring 3 is sampled by the amplifier circuit 50, and the sampled electric signal and If the sixth threshold is compared with the sixth threshold, the start of radiation irradiation is detected. Thus, since the start of radiation irradiation can be detected only by changing the driving method, it is not necessary to provide a configuration for detecting the start of radiation irradiation. For example, a special TFT switch 4 is designed or an additional circuit is provided. There is no need.

[Seventh Embodiment]
Next, a seventh embodiment will be described. In the present embodiment, the description of the configuration and operation substantially the same as those of the above-described embodiment will be omitted. In the radiation image detector 100 of the present embodiment, since the detection method of the start of radiation irradiation is different from the above-described embodiment, the detection method of the start of radiation irradiation will be described.

  In the radiation image detector 100 of the present embodiment, each pixel 20 includes a plurality of TFT switches 4, and the TFT switch 4 to be used is changed depending on the detection of the start of radiation irradiation and the radiographic image capturing. Control as follows. FIG. 28 is a configuration diagram showing an example of the overall configuration of the radiation image detector 100 of the present embodiment.

  As shown in FIG. 28, each pixel 20 of the radiation image detector 100 of the present embodiment includes two TFT switches 4 (4A, 4B). The TFT switch 4A is driven by a drive signal that flows through the scanning wiring 101 (G1A, G2A, G3A, G4A), and is driven to an ON state when reading out charges for generating a radiation image from the sensor unit 103. On the other hand, the TFT switch 4B is driven by a drive signal flowing through the scanning wiring 101 (G1B, G2B, G3B, G4B), and is driven out of the on-field when reading out the charge from the sensor unit 103 when detecting the start of radiation irradiation. The In the radiographic image capturing pixel 20 </ b> A, the TFT switch 4 </ b> A is connected to the signal wiring 3, but the TFT switch 4 </ b> B is not connected to the signal wiring 3. In the radiation detection pixel 20B, both the TFT switch 4A and the TFT switch 4B are connected to the signal wiring 3.

  The imaging process of this embodiment will be described. In the present embodiment, since steps (processes) that are substantially the same as the shooting process (see FIG. 7) of the first embodiment are included, the fact that the steps (processes) are substantially the same is described. Detailed description is omitted. FIG. 29 shows a flowchart of an example of the flow of the entire imaging process in the radiation image detector 100 of the present embodiment.

  In step 1000, the scanning wiring driving circuit 104 is instructed to output a driving signal for reset driving the TFT switch 4A, and the scanning wiring driving circuit 104 is instructed to output a driving signal (gate-on signal) to the TFT switch 4B. To do.

  Hereinafter, Step 1001 to Step 1024 correspond to Step 100 to Step 124 of the photographing processing according to the first embodiment, respectively. Step 1001 corresponds to step 100 of the imaging process of the first embodiment, and starts driving the amplifier circuit 50 (amplifier 52) of the signal detection circuit 105 to continuously drive it. As a result, the charge is read from the radiation detection pixel 20B by the TFT switch 4B, and an electric signal corresponding to the irradiation of the radiation flows to the signal wiring 3 and is sampled by the amplifier circuit 50 (amplifier 52). In the radiographic image capturing pixel 20A, since the TFT switch 4B is not connected to the signal wiring 3, an electrical signal is transmitted from the TFT switch 4B to the signal wiring 3 regardless of whether a gate-on signal is applied to the TFT switch 4B. Will not be read.

  In the next step 1002, the control unit 106 compares the electric signal corresponding to the electric charge sampled by the amplifier circuit 50 with the seventh threshold value or more, and whether or not radiation irradiation is started depending on whether or not the seventh signal is exceeded. Detect whether or not. The seventh threshold value may be obtained in advance as a threshold value for starting radiation irradiation through experiments or the like.

  If the electrical signal is less than the seventh threshold, it is denied and enters a standby state. On the other hand, if it is greater than or equal to the seventh threshold, since the start of radiation irradiation has been detected, the determination is affirmative and the routine proceeds to step 1003. In step 1003, a gate-off signal is output to the TFT switch 4A and the TFT switch 4B, and charge accumulation by each pixel 20 is started. Steps 1004 to 1018 for detecting noise after the start of charge accumulation are substantially the same as steps 104 to 118 in the first embodiment. The presence / absence, intensity, and generation period of noise are detected based on the change over time of the electrical signal, and the detection result and the radiation image are displayed based on the detection result. In this embodiment, a gate-on signal is output to both the TFT switch 4A and the TFT switch 4B in step 1014 when the radiation image is not displayed (when noise having a high intensity and a long generation period is detected). The charge accumulated in the pixel 20 is reset.

  Steps 1020 to 1024 for capturing a radiation image are substantially the same processes as steps 120 to 124 in the first embodiment. When the accumulation time elapses, the charges are sequentially read from the pixels 20. At this time, in this embodiment, a gate-on signal is output to the TFT switch 4A, and an electric signal corresponding to the electric charge accumulated by the TFT switch 4A is read out to the signal wiring 3. In the present embodiment, at this time, charges are read from both the radiation image capturing pixel 20A and the radiation detection pixel 20B. The control unit 106 generates a radiation image based on the acquired electrical signal. Furthermore, after outputting to the control apparatus 202 so that the produced | generated radiographic image may be displayed, this process is complete | finished.

  Thus, in the present embodiment, each pixel 20 includes a radiation image capturing TFT switch 4A and a radiation irradiation start detection TFT switch 4B. When detecting the start of radiation irradiation, the start of radiation irradiation is detected based on the electrical signal output from the radiation detection pixel 20B to the signal wiring 3 by the TFT switch 4B. Further, when capturing a radiation image, an electrical signal output to the signal wiring 3 is acquired by the TFT switch 4A of the radiation image capturing pixel 20A and the radiation detection pixel 20B to generate a radiation image. As a result, when detecting the start of radiation irradiation, the signal intensity can be increased as compared with the case of using the leakage current described in the sixth embodiment, so that the S / N ratio is improved. The In addition, since the radiation loss time from when radiation irradiation is actually started to when the irradiation start is detected can be reduced, charge loss due to reset driving can be ignored. In addition, since the radiation image can be generated by the electric charges (electric signals) read from the radiation image capturing pixel 20A and the radiation detection pixel 20B, the radiation detection pixel 20B does not become a defective pixel, and the radiation image It is possible to suppress the occurrence of image defects.

  In the present embodiment, all the pixels 20 are configured to include the TFT switch 4A and the TFT switch 4B. However, the present invention is not limited to this, and the radiation detection pixel 20B includes both TFT switches 4 (4A, 4B). It only has to have. Note that it is preferable that all the pixels 20 include the FT switch 4 </ b> A and the TFT switch 4 </ b> B from the viewpoint of manufacturing the radiation image detector 100.

  In each of the above-described embodiments, detection related to noise is performed by the control unit 106 of the radiation image detector 100, but is not limited thereto, and may be performed by the control unit 210 of the control device 202, for example.

  Further, in each of the above-described embodiments, detection regarding noise is performed using each threshold value. However, the present invention is not limited to this. For example, detection is performed based on the waveform of an electric signal, the time between peaks of a predetermined period, or the like. May be. Moreover, in each embodiment mentioned above, although the signal analysis is performed by the differentiation process of an electric signal and the difference with a moving average, it is not restricted to this, You may perform another signal analysis process. Note that the differential process has a high resolution, and for example, it is preferable to perform the differential process because it can be appropriately separated even when the radiation irradiation timing and the noise generation timing overlap.

  The detection of the start of radiation irradiation is not limited to the above-described embodiment, and is not particularly limited as long as the start of radiation irradiation is detected. For example, the radiation detection pixels 20 may be provided separately, or some of the radiation image capturing pixels 20A may be used. In the above-described embodiment, detection is performed by comparison with the first threshold value. However, the detection is not limited to this, and detection may be performed based on whether a predetermined condition is satisfied as a radiation irradiation start condition. Well, not particularly limited.

  In each of the above-described embodiments, the case where the radiation image is displayed on the display unit 212 of the control device 202 has been described. However, the present invention is not limited to this. For example, the display unit 212 displays the radiation image on an external display device other than the control device 202. May be.

  In each of the above-described embodiments, the case of the indirect conversion method has been described. However, the present invention is not limited to this, and the present invention may be applied to the case of a direct conversion method in which radiation is directly converted into charges in a semiconductor layer and stored. In this case, the radiation detection element in the direct conversion method generates charges when irradiated with radiation.

  In addition, the configurations and operations of the radiation image detector 100 and the radiation detector 10 described in the present embodiment are merely examples, and can be changed according to the situation without departing from the gist of the present invention. Needless to say.

  Moreover, in this Embodiment, the radiation of this invention is not specifically limited, X-ray, a gamma ray, etc. can be applied.

4 TFT switch, 4A TFT switch for radiographic imaging, 4B TFT switch for detection of radiation irradiation start 10 Radiation detector 20 pixels, 20A Radiographic imaging pixels, 20B Radiation detection pixel 20B
Reference Signs List 70 detector 100 radiation image detector 103 sensor unit 104 scanning wiring drive circuit 105 signal detection circuit 106, 210 control unit 108, 213 notification unit 200 radiation image imaging system 201 radiation image imaging device 202 control device 204 radiation irradiation device

Claims (31)

A plurality of pixels each including a sensor unit that generates a charge according to the dose of irradiated radiation, stores the generated charge, and a switch element that reads the charge generated in the sensor unit and outputs it to a signal wiring;
Detecting means for detecting the start of irradiation when an electrical signal corresponding to the electric charge generated by radiation irradiation satisfies a predetermined irradiation detection condition;
After detecting the start of irradiation by said detecting means, Tokushi preparative an electrical signal corresponding to the charges read out from the pixels, it is determined whether those electrical signal comprises an electrical signal caused by noise, the noise Control means for controlling the notification means so as to notify when the resulting electrical signal is included;
A radiographic imaging apparatus comprising: After detecting the start of irradiation by said detecting means, said control means, said sensor unit to start accumulation of electric load, the said electric signal is judged whether comprising an electrical signal caused by noise after storage start,
The radiographic imaging device according to claim 1. Wherein, after detecting the start of irradiation by said detecting means, and an electric signal obtained, a predetermined et condition for a predetermined condition and noise generation period detection for intensity detection of the noise , based on, detects the intensity and generation period of the noise, based on the detected intensity and occurs period, it is determined whether to output the radiation image,
The radiographic imaging apparatus of Claim 1 or Claim 2. In the case where at least one of the case where it is detected that the intensity of the noise is weak and the case where the generation period is short is determined, the control means determines to output the radiation image.
The radiographic imaging device according to claim 3 . When the control means detects that the noise intensity is strong and the generation period of noise is long, the control means determines not to output the radiation image.
The radiographic imaging apparatus of Claim 3 or Claim 4 . The control means acquires an electric signal corresponding to the charge for each predetermined region according to the plurality of pixels, and the electric signal includes an electric signal caused by noise for the predetermined region. To judge,
The radiographic imaging device of any one of Claims 1-5. The control means informs the predetermined area determined to include an electrical signal due to noise ,
The radiographic imaging apparatus according to claim 6 . The control means determines whether to output a radiographic image based on the position of the predetermined area determined to include an electrical signal due to noise ,
The radiographic imaging apparatus of Claim 6 or Claim 7 . The control means determines that the position of the area where the predetermined determining that include electric signal due to noise, if a predetermined position as a central for the entire region, does not output the radiation image image To
The radiographic imaging apparatus according to claim 8 . The control means, based on the time change of the acquired electrical signal, determines that the electrical signal includes an electrical signal caused by noise when the electrical signal exceeds a noise detection threshold;
The radiographic imaging apparatus of any one of Claims 1-9. It said control means, based on the electric signal obtained by differentiating processing a temporal change in the acquired electrical signal, in the event that the electrical signal exceeds the noise detection threshold is determined to contain an electrical signal due to noise,
The radiographic imaging apparatus according to claim 10 .   The control means calculates a time moving average based on the time change of the acquired electrical signal, and calculates it. Based on the difference in the electrical signal at the time of determination as the time moving average issued, the difference is When it exceeds the threshold for detection of noise, it is determined that it contains an electrical signal caused by noise.
  The radiographic imaging apparatus according to claim 10.   The control means compares the acquired electric signal with an intensity detection threshold value to determine the strength of the noise. Detect the degree,
  The radiographic imaging apparatus of any one of Claims 3-12.   The control means is based on the number of times the acquired electrical signal has reached the occurrence time detection threshold, Detecting the noise generation period;
  The radiographic imaging apparatus of any one of Claims 3-13.   The notification means is provided in a radiation image detector including the plurality of pixels.
  The radiographic imaging device of any one of Claims 1-14.   The notification means is provided outside a radiation image detector including the plurality of pixels.   The radiographic imaging apparatus of any one of Claims 1-15.   The plurality of pixels include radiation image capturing pixels and radiation detection pixels, and the detection unit Radiation irradiation based on an electrical signal corresponding to the electric charge output from the radiation detection pixel When the start is detected, the control means detects a charge corresponding to the electric charge read from the radiation detection pixel. Get a qi signal,
  The radiographic imaging apparatus of any one of Claims 1-16.   The switch element of the radiation image capturing pixel is connected to the signal wiring based on a control signal. The radiation detection pixel outputs a charge to the signal wiring regardless of the control signal. Output,
  The radiographic imaging apparatus of Claim 17.   The radiation detection pixel is a radiation driven based on a control signal flowing through the first scanning wiring. The image sensor is driven based on a switch element for image capturing and a control signal flowing through the second scanning wiring. Including a switch element for detecting radiation, and the detecting means includes a switch element for detecting radiation. The start of radiation irradiation is detected based on the electrical signal corresponding to the electric charge read by driving, and the previous The control means includes an electrical signal corresponding to the charge read from the radiation detection pixel, and the Charges read out by driving the radiation image capturing switch element of the radiation detection pixel To obtain an electrical signal according to
  The radiographic imaging apparatus of Claim 17.   The radiation image capturing pixel includes the radiation image capturing switch element and the radiation. Including a switch element for detection, and the switch element for radiation detection is not connected to the signal wiring. A continuation,
  The radiographic imaging apparatus of Claim 19.   A bias voltage applied from a bias power supply is supplied to the sensor units of the plurality of pixels. A bias line;
  Charge detection means for detecting charge flowing in the bias line;
The detection means includes a radiation irradiator based on a change in the charge detected by the charge detection means. Detect the start of shooting,
  The radiographic imaging apparatus of any one of Claims 1-16.   During the detection period in which the detection means detects the start of the radiation irradiation, the switch element is turned off State
  The radiographic image capturing apparatus according to claim 21.   In the detection period, the detection of the start of radiation irradiation is interrupted every predetermined time, and the switch element is The child is turned on, and the charge generated in the sensor unit is read and output to the signal wiring. After that, the switch element is turned off, and the detection of the start of radiation irradiation is resumed.
  The radiographic imaging apparatus of Claim 22.   The predetermined irradiation detection condition is a condition predetermined by an irradiation detection threshold. The
  The radiographic image capturing device according to any one of claims 1 to 23.   The control means reads from the pixels for each predetermined region according to the plurality of pixels. An electric signal corresponding to the generated electric charge is acquired, and the electric signal is neutralized for each of the predetermined areas. If there is an electrical signal due to noise, The image and the predetermined area determined to include an electrical signal caused by noise. And control to store the information in association with at least one of the internal or external of the device. Carry out
  25. The radiographic image capturing apparatus according to any one of claims 1 to 24.   An amplifier that samples an electrical signal corresponding to the electric charge read from the sensor unit is further provided. In preparation for
  After the detection unit detects the start of radiation irradiation, the control unit applies power to the sensor unit. Load accumulation starts, and after the accumulation starts, does the electrical signal contain an electrical signal due to noise? If it is determined that an electric signal caused by noise is included, the amplifier is sampled. The detected charge is reset and the detection means starts detecting the start of radiation irradiation again. The
  The radiographic image capturing apparatus according to any one of claims 1 to 25.   After the detection unit detects the start of radiation irradiation, the control unit applies power to the sensor unit. Load accumulation starts, and after the accumulation starts, does the electrical signal contain an electrical signal due to noise? If it is determined that an electrical signal due to noise is included, shooting is stopped.
  The radiographic image capturing apparatus according to any one of claims 1 to 25.   After the detection unit detects the start of radiation irradiation, the control unit applies power to the sensor unit. Load accumulation starts, and after the accumulation starts, does the electrical signal contain an electrical signal due to noise? If it is determined that an electrical signal caused by noise is included, radiation irradiation is stopped. ,
  The radiographic image capturing apparatus according to any one of claims 1 to 25.   A radiation irradiation device;
  The radiographic image is taken with the radiation irradiated from the radiation irradiation device. A radiographic imaging device according to any one of claims 28,
  Radiographic imaging system equipped with.   A sensor unit that generates a charge in response to the irradiated radiation and accumulates the generated charge; and A plurality of switch elements each provided with a switch element for reading out the electric charge generated in the sensor unit and outputting it to the signal wiring And an electrical signal corresponding to the electric charge generated by radiation irradiation is determined in advance. Detecting means for detecting the start of radiation irradiation when the condition is satisfied, and radiation irradiation by the detecting means After detecting the start, an electric signal corresponding to the electric charge read from the pixel is acquired, and the electric Judgment is made if the electric signal contains an electric signal caused by noise, and if the electric signal contains an electric signal caused by noise. Control means for controlling the notification means so as to notify Control program for radiographic imaging apparatus for causing computer to function as control means .   A sensor unit that generates a charge in response to the irradiated radiation and accumulates the generated charge; and A plurality of switch elements each provided with a switch element for reading out the electric charge generated in the sensor unit and outputting it to the signal wiring When taking a radiographic image with a radiographic imaging device equipped with
  An electrical signal corresponding to the charge generated by radiation irradiation satisfies a predetermined irradiation detection condition. A detection process for detecting the start of radiation in the case of
  After detecting the start of radiation irradiation in the detection step, it responds to the charges read from the pixels. And determine whether the electrical signal contains an electrical signal caused by noise. A control step of controlling the notification means so as to notify when an electrical signal resulting from the error is included;
  A method for controlling a radiographic imaging apparatus comprising: