JP2014122903A - Radiation detector and radiation imaging device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To suppress the manufacturing cost as compared with conventional techniques.SOLUTION: A radiation detector 10A includes: a scintillator 70 for converting applied radiation into visible light; a TFT array substrate 72 with photosensors having a first surface being an incident side of radiation, and a second surface different from the first surface, and having, on the first surface side, multiple pixels for detecting radiation, in a matrix, for storing electric charge generated by radiation of the visible light from the scintillator provided on the first surface side, and each having a switch element for reading out the stored electric charge; and a photosensor array substrate 74 for AEC (automatic exposure control) provided on the second surface side of a first substrate, and having multiple sensors for detecting the amount of radiation doses, in a matrix, for generating electric charge by being irradiated with visible light.

Description

  The present invention relates to a radiation detector, and in particular, accumulates charges generated by irradiating a plurality of pixels arranged in a matrix form with radiation to be detected, and detects the accumulated charge amount as information indicating an image. The present invention relates to a radiation detector and a radiographic imaging apparatus having the radiation detector.

  In recent years, an X-ray sensitive layer is arranged on a TFT (Thin film transistor) active matrix substrate, and a radiation detector (radiation detection element) such as an FPD (flat panel detector) capable of directly converting X-ray information into digital data has been used. Radiographic imaging devices (radiological image detection devices) have been put into practical use. Compared with conventional imaging plates, this FPD has the advantage that images can be confirmed instantly and moving images can be confirmed, and is rapidly spreading.

  Various types of radiation detection elements of this type have been proposed. For example, a direct conversion method in which radiation is directly converted into electric charges in a semiconductor layer and stored, or radiation is once converted into CsI: Tl, GOS (Gd2O2S). There is an indirect conversion method in which the light is converted into light by a scintillator such as Tb), and the converted light is converted into electric charges in a semiconductor layer and accumulated.

  Here, a technique is known in which a total dose of radiation to be irradiated is detected using an AEC sensor, and a radiation source for irradiating the radiation is controlled (see, for example, Patent Document 1). In the technique described in Patent Document 1, an AEC sensor (second radiation conversion element) is formed in a gap between first radiation conversion elements (elements for radiation detection), and the first radiation conversion element is formed. An AEC sensor is formed on the same substrate as the formed substrate.

Japanese Patent No. 4217506

  As described above, in the technique described in Patent Document 1, an AEC sensor is built on a substrate on which a plurality of first radiation conversion elements, which are expensive components, are provided in a matrix, and is manufactured using the AEC sensor or its wiring. When a defect occurs, the entire board becomes a defective product. That is, when a manufacturing failure occurs in the AEC sensor or its wiring, it is necessary to discard the entire board even if no manufacturing failure occurs in the first radiation conversion element provided in a matrix. There was a problem that it was expensive. Here, since a substrate in which an AEC sensor is incorporated and a plurality of first radiation conversion elements are provided in a matrix is subjected to shipping inspection upon completion, the yield of the substrate can be expressed by the following equation (1).

Yield = non-defective rate of first radiation conversion element x non-defective rate of AEC sensor (1)
The present invention has been made to solve the above-described problems, and an object of the present invention is to provide a radiation detector that can reduce the manufacturing cost as compared with the prior art.

  In order to achieve the above object, a radiation detector according to the present invention includes a scintillator that converts irradiated radiation having a first wavelength into visible light having a wavelength longer than the first wavelength, and a radiation incident side. The first surface has a second surface different from the first surface, and accumulates and accumulates charges generated by irradiation with visible light from a scintillator provided on the first surface side. A plurality of radiation detection pixels each provided with a switch element for reading out charges are provided in a matrix on the first surface side, and a control signal for switching each switch element provided in each radiation detection pixel flows. A first substrate provided on a first surface side with a plurality of scanning wirings and a plurality of signal wirings through which an electrical signal corresponding to the electric charge accumulated in the radiation detection pixel flows according to a switching state of each switch element; The second A plurality of radiation dose detection sensors which are provided on the second surface side of the substrate and generate charges when irradiated with the visible light irradiated on the first surface and emitted from the second surface. And a second substrate provided in a matrix. A plurality of radiation dose detection sensors provided in a matrix are provided on the entire surface of the second substrate, and each of the plurality of radiation dose detection sensors is connected to each of the radiation dose detection wirings. An electrical signal corresponding to the charge generated in the connected radiation dose detection sensor flows through each of the radiation dose detection wires, and each of the radiation dose detection wires emits radiation of the first wavelength. It is connected to a radiation irradiation control device that detects the amount and controls the irradiation of the first wavelength radiation by the radiation source that irradiates the first wavelength radiation based on the irradiation amount.

  In the present invention, the scintillator converts the irradiated radiation having the first wavelength into visible light having a wavelength longer than the first wavelength. The first substrate has a first surface on the radiation incident side and a second surface different from the first surface. On the first surface of the first substrate, a plurality of radiation detecting elements each provided with a switch element for accumulating charges generated by irradiation of visible light from the scintillator and reading the accumulated charges Pixels are provided in a matrix. Further, the radiation on the first surface of the first substrate depends on a plurality of scanning wirings through which a control signal for switching each switch element provided in each radiation detection pixel flows and the switching state of each switch element. A plurality of signal wirings through which an electric signal corresponding to the electric charge accumulated in the detection pixel flows are provided. The second substrate is provided on the second surface side of the first substrate, and the second substrate is irradiated on the first surface side of the first substrate and emitted from the second surface. A plurality of radiation dose detection sensors that generate charges when irradiated with visible light are provided in a matrix.

  As described above, according to the present invention, since the radiation detection pixel and the radiation irradiation amount detection sensor are provided on different substrates, the yield of the radiation detection pixel and the yield of the radiation irradiation amount detection sensor are increased. For example, even if a manufacturing defect occurs in the radiation dose detection sensor, only the second substrate is a defective product, and the first substrate is not a defective product. That is, even if a manufacturing defect occurs in the radiation dose detection sensor, the first substrate on which a plurality of radiation detection pixels are provided in a matrix form does not need to be subjected to disposal or the like.

  Therefore, according to the present invention, it is possible to reduce the manufacturing cost as compared with the prior art.

  Further, according to the present invention, since the radiation dose detection sensor is not provided between the radiation detection pixels, the AEC sensor (second sensor) is disposed in the gap between the first radiation conversion elements (elements for radiation detection). Compared with the prior art in which the radiation conversion element is formed, the effective detection area of the radiation detection pixel can be expanded, and the accuracy of radiation detection is improved.

  Further, since the second substrate on which a plurality of radiation dose detection sensors are arranged is provided on the second surface side of the first substrate on which a plurality of radiation detection pixels are provided in a matrix, for example, More radiation (for example, light) of the second wavelength can be received than when the AEC sensor is formed in the gap between the radiation detection TFTs, and the detection sensitivity becomes higher. This is because when the AEC sensor is formed in the gap of the TFT, the sensor part of the AEC sensor having a smaller area than the gap provided with the AEC sensor receives the radiation of the second wavelength. In the present invention, since the AEC sensor is disposed on the upper surface of the TFT, the AEC sensor can be disposed in the entire gap of the TFT, and more radiation of the second wavelength emitted from the gap can be received. is there.

  In addition, since the light converted by the same scintillator is detected by the radiation detection pixel and the radiation irradiation amount detection sensor, image detection and radiation according to the irradiation conditions are compared with the case where the irradiation amount detection is performed by the external AEC sensor. It is possible to reduce the deviation of the irradiation amount detection.

  In the radiation detector according to the present invention, the area of each of the plurality of radiation dose detection sensors may be configured to be larger than the area of each of the plurality of radiation detection pixels.

  In the radiation detector according to the present invention, a plurality of radiation detection pixels may be provided in a matrix in a region where a plurality of radiation dose detection sensors provided in a matrix are formed. .

  Moreover, the radiation detector which concerns on this invention WHEREIN: The reflector which is a member for reflecting light may be provided in the surface on the opposite side to the surface which contact | connects the 1st surface of a scintillator.

  In the radiation detector according to the present invention, the second substrate may include a resin substrate.

  In the radiation detector according to the present invention, the radiation dose detection sensor may include an organic material.

  In the radiation detector according to the present invention, the radiation dose detection sensor may include an inorganic material.

  Further, in the radiation detector according to the present invention, the scintillator may include GOS.

  In the radiation detector according to the present invention, the scintillator may include CsI.

  In addition, the radiographic imaging apparatus according to the present invention includes a scintillator that converts irradiated radiation having a first wavelength into visible light having a wavelength longer than the first wavelength, a first surface that is a radiation incident side, and A second surface different from the first surface, for accumulating charges generated by irradiating visible light from a scintillator provided on the first surface side and for reading the accumulated charges A plurality of radiation detection pixels each provided with a switch element are provided in a matrix on the first surface side, and a plurality of scanning wirings through which a control signal for switching each switch element provided in each radiation detection pixel flows A first substrate provided on the first surface side with a plurality of signal wirings through which an electrical signal corresponding to the charge accumulated in the radiation detection pixel according to the switching state of each switch element; and the first substrate Second of A plurality of radiation dose detection sensors that are provided on the surface side and generate charges when irradiated with visible light emitted from the second surface and emitted from the first surface are provided in a matrix. A plurality of radiation dose detection sensors provided in a matrix and provided on the entire surface of the second substrate, and each of the plurality of radiation dose detection sensors is used for radiation dose detection. An electrical signal corresponding to the charge generated in the connected radiation dose detection sensor flows to each of the radiation dose detection wirings, and each of the radiation dose detection wirings is connected to each of the wirings. Is connected to a radiation irradiation control device that detects radiation dose of the first wavelength and controls radiation of the first wavelength by the radiation source that emits radiation of the first wavelength based on the radiation dose. A radiation detector; Comprising a radiation source for incident from the first surface side of the first substrate ray, a.

  Thus, according to the present invention, compared with the prior art, there is an excellent effect that the manufacturing cost can be suppressed.

It is a block diagram of the radiation detector of the radiographic image detection apparatus which concerns on 1st Embodiment. It is a block diagram of the radiation detector of the radiographic image detection apparatus which concerns on 1st Embodiment. It is a top view which shows the structure of the radiation detector which concerns on 1st Embodiment. It is a line sectional view of a radiation detector concerning a 1st embodiment. It is a block diagram of the radiation detector which concerns on 1st Embodiment. It is a figure for demonstrating an example of the manufacturing process of the radiation detection element of the TFT array substrate with a photosensor which concerns on 1st Embodiment. It is a figure which shows an example of the sheet-like photosensor array which concerns on 1st Embodiment. It is a figure which shows an example of the photoelectric converting film containing the organic thin film material which concerns on 1st Embodiment. It is a schematic diagram of the TFT array substrate with photosensor and the photosensor array substrate for AEC according to the first embodiment. It is a block diagram of the radiation detector of the radiographic image detection apparatus which concerns on 2nd Embodiment. It is a figure which shows the outline of the manufacturing method of the radiographic image detection apparatus of 2nd Embodiment. It is sectional drawing of the thing manufactured at each step of the manufacturing method of 2nd Embodiment. It is a block diagram of the radiation detector of the radiographic image detection apparatus which concerns on 2nd Embodiment.

Hereinafter, embodiments for carrying out the present invention will be described with reference to the drawings.
[First Embodiment]
First, the first embodiment will be described. In the present embodiment, the present invention is applied to an indirect conversion type radiation detector 10A that once converts radiation of the first wavelength into radiation of the second wavelength and converts the converted radiation of the second wavelength into electric charge. The case will be described. In the following description, the radiation having the first wavelength is simply referred to as “radiation (for example, X-ray)”, and the radiation having the second wavelength different from the first wavelength is “light”. However, the radiation of the first wavelength and the radiation of the second wavelength are not limited to this.

  1 and 2 show the overall configuration of a radiographic image capturing apparatus (radiological image detection apparatus) 100 using the radiation detector 10A according to the first exemplary embodiment. In FIG. 2, the scintillator 70 and the AEC photosensor array substrate 74 are omitted.

  The radiographic image capturing apparatus 100 according to the present embodiment includes an indirect conversion type radiation detector 10A.

  The radiation detector 10A includes a scintillator 70, a TFT array substrate 72 with a photosensor, and an AEC photosensor array substrate 74.

  First, the scintillator 70 will be described. The scintillator 70 converts the irradiated radiation into light and emits the light. As shown in FIG. 1, a reflector, which is a member for reflecting light, is provided below the scintillator 70 of the present embodiment. The scintillator 70 corresponds to the wavelength conversion unit (wavelength conversion layer) of the present invention.

  Next, the TFT array substrate 72 with a photo sensor will be described.

  The TFT array substrate 72 with a photo sensor includes an upper electrode, a semiconductor layer, and a lower electrode, which will be described later. The sensor unit 103 receives light obtained by converting irradiated radiation by a scintillator, and stores the charge in the sensor unit 103. A number of pixels each including a TFT switch 4 for reading out the generated charges are provided in a two-dimensional manner.

  Further, on the TFT array substrate 72 with a photo sensor, a plurality of scanning wirings 101 for turning on / off the TFT switch 4, a plurality of signal wirings 3 for reading out charges accumulated in the sensor unit 103, Are provided so as to cross each other.

  An electric signal corresponding to the amount of electric charge accumulated in the sensor unit 103 flows through each signal line 3 when any TFT switch 4 connected to the signal line 3 is turned on. Each signal wiring 3 is connected to a signal detection circuit 105 that detects an electric signal flowing out to each signal wiring 3, and each scanning wiring 101 is used to turn on / off the TFT switch 4 in each scanning wiring 101. A scan signal control device 104 for outputting the control signal is connected.

  The signal detection circuit 105 includes an amplification circuit for amplifying an input electric signal for each signal wiring 3. The signal detection circuit 105 detects the amount of electric charge accumulated in each sensor unit 103 as information of each pixel constituting the image by amplifying and detecting the electric signal input from each signal wiring 3 by the amplification circuit. To do.

  The signal detection circuit 105 and the scan signal control device 104 perform predetermined processing on the electrical signal detected by the signal detection circuit 105 and output a control signal indicating signal detection timing to the signal detection circuit 105. The signal processing device 106 is connected to the scan signal control device 104 for outputting a control signal indicating the output timing of the scan signal.

  Next, the photosensor-equipped TFT array substrate 72 according to the present embodiment will be described in more detail with reference to FIGS. FIG. 3 is a plan view showing the structure of one pixel unit of the radiation detection element on the TFT array substrate 72 with a photosensor according to this embodiment, and FIG. FIG. 4B is a cross-sectional view taken along the line BB of FIG. 3.

  As shown in FIGS. 4A and 4B, the radiation detection element of this embodiment has a scanning wiring 101 and a gate electrode 2 formed on an insulating substrate 1 made of non-alkali glass or the like. The scanning wiring 101 and the gate electrode 2 are connected (see FIG. 3). 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 the scanning wiring 101 and the gate electrode 2 so as to cover the scanning wiring 101 and the gate electrode 2, and a portion located on the gate electrode 2 acts as a gate insulating film in the TFT switch 4. To do. 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, together with the source electrode 9 and the drain electrode 13, a signal wiring 3 and a common electrode wiring 25 are formed in parallel with the signal wiring 3. The source electrode 9 is connected to the signal wiring 3. The wiring layer in which the signal wiring 3, the source electrode 9, and the common electrode wiring 25 are formed (hereinafter, this wiring layer is also referred to as “second signal wiring layer”) is mainly Al or Cu, or Al or Cu. However, the present invention is not limited to these.

  A contact layer (not shown) is formed between the source electrode 9 and the drain electrode 13 and the semiconductor active layer 8. This contact layer is made of an impurity-doped semiconductor such as impurity-doped amorphous silicon. These constitute the TFT switch 4 for switching.

Then, the semiconductor active layer 8, the source electrode 9, the drain electrode 13, the signal wiring 3, and the common electrode wiring 25 are covered. A protective film layer 11 is formed. The TFT protective film layer 11 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 11. This interlayer insulating film 12 is made of a photosensitive organic material having a low dielectric constant (relative dielectric constant ε _r = 2 to 4) (for example, a positive photosensitive acrylic resin: a copolymer of methacrylic acid and glycidyl methacrylate). And a base polymer mixed with a naphthoquinonediazide-based positive photosensitive agent). In the radiation detection element 10 according to the present exemplary embodiment, the capacitance between metals disposed in the upper layer and the lower layer of the interlayer insulating film 12 is kept low by the interlayer insulating film 12. In general, such a material also has a function as a flattening film, and has an effect of flattening a lower step. Thereby, since the shape of the semiconductor layer 6 disposed in the upper layer is flattened, it is possible to suppress a decrease in absorption efficiency due to the unevenness of the semiconductor layer 6 and an increase in leakage current. In the interlayer insulating film 12 and the TFT protective film layer 11, a contact hole 16 and a contact hole 22A are formed at a position facing the drain electrode 13 and a position on the irradiation surface side of the region where the scanning wiring 101 is formed. ing.

  A lower electrode 14 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 16, and the lower electrode 14 is connected to the drain electrode 13 of the TFT switch 4. ing. If the semiconductor layer 6 described later is as thick as about 1 μm, the material of the lower electrode 14 is not limited 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 (indium tin oxide).

  On the other hand, when the film thickness of the semiconductor layer 6 is thin (around 0.2 to 0.5 μm), light is not sufficiently absorbed by the semiconductor layer 6, 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 6 that functions as a photodiode is formed on the lower electrode 14. In the present embodiment, a photodiode having a PIN structure is employed as the semiconductor layer 6, and an n ⁺ layer, an i layer, and a p ⁺ layer are sequentially stacked from the lower layer. In the present embodiment, the lower electrode 14 is made larger than the semiconductor layer 6. When the semiconductor layer 6 is thin (for example, 0.5 μm or less), a light shielding metal is disposed to cover the TFT switch 4 in order to prevent light from entering the TFT switch 4. preferable.

  Preferably, in order to suppress light entering the TFT switch 4 due to irregular reflection of light inside the device, a space from the channel portion of the TFT switch 4 to the end portion of the lower electrode 14 made of a light shielding metal is secured to 5 μm or more. .

  A protective insulating film 17 is formed on the interlayer insulating film 12 and the semiconductor layer 6 so that each semiconductor layer 6 has an opening. An upper electrode 7 is formed on the semiconductor layer 6 and the protective insulating film 17 so as to cover at least the opening of the protective insulating film 17. For the upper electrode 7, for example, a material having high light transmittance such as ITO or IZO (zinc oxide indium) is used. The upper electrode 7 also serves as a conductive member connected to the common electrode wiring 25 that is disposed in the lower layer and supplies a bias voltage to the upper electrode 7. As shown in FIG. 3B, the common electrode wiring 25 is connected to a contact pad 24 formed in the layer of the lower electrode 14 through a contact hole 22A provided in the first interlayer insulating film 12, and By covering the contact hole 22 </ b> B provided in the protective insulating film 17 with the upper electrode 7, the upper electrode 7 and the common electrode wiring 25 are electrically connected.

  Here, the upper electrode 7 and the conductive member connected to the common electrode wiring 25 may be formed of different layers of metal.

  In this way, radiation detection pixels (radiation detection pixels) are formed on the first surface 1A ′ side of the substrate 1, and the photosensor-equipped TFT array substrate 72 thus formed is shown in FIG. As described above, the scintillator 70 made of GOS or the like is attached to the first surface 1A ′ side using an adhesive resin 28 having a low light absorption property on which radiation detection pixels are formed. As shown in the figure, an AEC photosensor array substrate 74 is provided on the surface 1B opposite to the first surface 1A '(surface 1B different from the first surface). . For the TFT array substrate 72 with a photosensor, the surface on the scintillator 70 side is referred to as a “first surface”, and the surface on the AEC photosensor array substrate 74 side is referred to as a “second surface”. The photosensor-equipped TFT array substrate 72 corresponds to the first substrate of the present invention, and the AEC photosensor array substrate 74 corresponds to the second substrate of the present invention.

  Next, with reference to FIGS. 6A to 6I, an example of a manufacturing process of the radiation detection element of the photosensor-equipped TFT array substrate 72 according to the first embodiment will be described.

  First, the gate electrode 2 and the scanning wiring 101 are formed on the substrate 1 as the first signal wiring layer (FIG. 6A). This first signal wiring layer is a laminated film with a barrier metal layer made of a low resistance metal such as Al or Al alloy or a refractory metal, and has a film thickness of about 100 to 300 nm on the substrate 1 by sputtering. Is deposited. Thereafter, the resist film is patterned by photolithography. Thereafter, the metal film is patterned by a wet etch method using an etchant for Al or a dry etch method. Then, the first signal wiring layer is completed by removing the resist.

  Next, an insulating film 15, a semiconductor active layer 8, and a contact layer (not shown) are sequentially deposited on the first signal wiring layer (FIG. 6B). The insulating film 15 is made of SiNx and has a thickness of 200 to 600 nm, the semiconductor active layer 8 is made of amorphous silicon and has a thickness of about 20 to 200 nm, and the contact layer is made of impurity-doped amorphous silicon and has a thickness of about 10 to 100 nm. Deposited by (Plasma-Chemical Vapor Deposition) method. Thereafter, similarly to the first signal wiring layer, resist patterning is performed by photolithography. Thereafter, the semiconductor active region is formed by selectively dry-etching the semiconductor active layer 8 and the contact layer made of the doped semiconductor with respect to the insulating film 15.

  Next, the signal wiring 3, the source electrode 9, the drain electrode 13, and the common electrode wiring 25 are formed as the second signal wiring layer on the insulating film 15 and the semiconductor active layer 8 (FIG. 6C). Similar to the first signal wiring layer, the second signal wiring layer is a laminated film with a barrier metal layer made of a low-resistance metal such as Al or an Al alloy or a refractory metal, or a single refractory metal film such as Mo. It consists of layers and the film thickness is around 100-300 nm. Similar to the first signal wiring layer, patterning is performed by photolithography, and the metal film is patterned by wet etching using an etchant for Al or dry etching. At this time, the insulating film 15 is not removed by selectively employing an etching method. A contact layer and a part of the semiconductor active layer 8 are removed by a dry etching method to form a channel region.

  Next, the TFT protective film layer 11 and the interlayer insulating film 12 are sequentially formed on the layer formed as described above (FIG. 6D). The TFT protective film layer 11 and the interlayer insulating film 12 are formed of a single inorganic material, formed by stacking a protective insulating film made of an inorganic material and an interlayer insulating film made of an organic material, or a single layer insulating film made of an organic material. It may be formed by layers. In the present embodiment, the electrostatic capacitance between the lower common electrode wiring 25 and the lower electrode 14 is suppressed, while the TFT protection composed of the photosensitive interlayer insulating film 12 and the inorganic material is used to stabilize the characteristics of the TFT switch 4. The film layer 11 has a laminated structure. For example, the TFT protective film layer 11 is formed by CVD film formation, a photosensitive interlayer insulating film 12 material, which is a coating system material, is applied, prebaked, and then passes through exposure and development steps. Thereafter, firing is performed to form each layer.

  Next, the TFT protective film layer 11 is patterned by photolithography (FIG. 6E). Note that this step is not necessary when the TFT protective film 11 is not disposed.

  Next, an Al-based material or a metal material such as ITO is deposited on the above layer by a sputtering method. The film thickness is around 20-200 nm. Patterning is performed by a photolithography technique, and patterning is performed by a wet etching method using a metal etchant or the like or a dry etching method to form the lower electrode 14 (FIG. 6F).

Next, n ⁺ , i, and p ⁺ layers are sequentially deposited from the lower layer by the CVD method to form the semiconductor layer 6 (FIG. 6G). The film thicknesses are n ⁺ layer 50-500 nm, i layer 0.2-2 μm, and p ⁺ layer 50-500 nm, respectively. The semiconductor layer 6 is completed by laminating each layer in order, patterning the semiconductor layer 6 by photolithography, and selectively etching with the lower interlayer insulating film 12 by dry etching or wet etching.

^Here, n ^{+, i,} was laminated in the order of ^{p +, p +, i,} and laminated in the order of ^{n +,} it may be a PIN diode.

  Next, a protective insulating film 17 made of a SiNx film is deposited by CVD or the like so as to cover the semiconductor layer 6. The film thickness is around 100 to 300 nm. Patterning is performed by a photolithography technique, and patterning is performed by a dry etching method to form an opening. (FIG. 6 (H)). Here, SiNx formed by CVD is described as an example, but any insulating material can be applied and is not limited to SiNx.

  Next, a connection portion between the upper electrode 7 and the common electrode wiring 25 is formed (FIG. 6I). A transparent electrode material such as ITO is deposited by sputtering on the upper layer of the layer formed as described above at the connection portion between the upper electrode 7 and the common electrode wiring 25. The film thickness is around 20-200 nm. Patterning is performed by a photolithography technique, and the upper electrode 7 is patterned by a wet etching method using an etchant for ITO or the like or a dry etching method. At this time, by selectively employing etching, the underlying protective insulating film 17 is not damaged.

  Finally, a GOS scintillator 70 and an AEC photosensor array substrate 74 are attached to the TFT array substrate 72 with a photosensor formed in this manner using an adhesive resin 28 or the like, as shown in FIG. Such a radiation detection element 10 is formed.

  Next, the AEC photosensor array substrate 74 will be described. The AEC photosensor array substrate 74 includes, for example, a resin substrate. The photo sensor array substrate 74 for AEC is provided on the “second surface” side of the TFT array substrate 72 with photo sensor, and the light converted by the scintillator 70 is shown on the photo sensor array substrate 74 for AEC. As shown in FIG. 1, one provided with a plurality of photosensors that generate charges by irradiating light emitted from the second surface and irradiated from the first surface side is used. That is, this photosensor is a radiation dose detection sensor. In addition, as such a photosensor, it is not necessary to detect light as finely as the TFT array. For example, a sheet-shaped photosensor array shown in FIG. 7 described in JP-A-9-307088 can be used. . Thereby, radiation dose detection (AEC) can be performed at low cost.

  In addition, such a photosensor layer contains an organic thin film material as shown in FIGS. 8A and 8B, for example, rather than a PIN-type or MIS-type photodiode using a-Si. A photoelectric conversion film is preferable. Compared to the case of using a PIN type photodiode or MIS type photodiode, it is more advantageous to use a photoelectric conversion film containing an organic thin film material in terms of reduction in manufacturing cost and flexibility. That's why. Note that a photoelectric conversion film containing an inorganic thin film material such as IGZO may be used for the photosensor layer.

  Each photosensor provided on the AEC photosensor array substrate 74 is used as a radiation dose detection sensor as described above, and is connected to each radiation dose detection wiring (see FIG. 9B). Has been. That is, an electrical signal corresponding to the electric charge generated in the connected photosensor flows through each of the radiation dose detection wirings. In addition, each of the photosensors is connected to a radiation irradiation control device (not shown) via each of the radiation irradiation amount detection wirings. Here, the radiation irradiation control device detects the radiation dose based on the electrical signal from the photosensor, and based on the detected radiation dose, the radiation source emits radiation (not shown). Control irradiation.

  As described above, in this embodiment, the scintillator 70 is provided on the first surface side of the TFT array substrate 72 with photosensor (see the schematic diagram shown in FIG. 9A), and the TFT array with photosensor is provided. An AEC photosensor array substrate 74 (see the schematic diagram shown in FIG. 9B) is provided on the second surface side of the substrate 72.

  Next, the operation principle of the radiation image detection apparatus 100 having the above structure will be described.

When X-rays are irradiated from above in FIG. 5 (FIG. 1), the irradiated X-rays are absorbed by the scintillator 70 and converted into visible light (second wavelength radiation). Note that X-rays may be irradiated from below in FIG. 5 (FIG. 1). In this case as well, the irradiated X-rays are absorbed by the scintillator 70 and converted into visible light. The amount of light generated from the scintillator 70 is 0.5 to ² μW / cm ² in normal medical diagnostic X-ray imaging. The generated light passes through the layer of the adhesive resin 28 and irradiates the semiconductor layer 6 of the sensor unit 103 arranged in an array on the TFT array substrate. A part of the generated light reaches the AEC photosensor array substrate 74, and the AEC photosensor array substrate 74 receives a part of the generated light.

In the radiation detector 10A, the semiconductor layer 6 is provided separately for each pixel unit. A predetermined bias voltage is applied to the semiconductor layer 6 from the upper electrode 7 through the common electrode wiring 25, and when light is irradiated, charges are generated inside. For example, in the case of a PIN structure in which the semiconductor layer 6 is laminated in the order of n ⁺ -ip ⁺ (n ⁺ amorphous silicon, amorphous silicon, p ⁺ amorphous silicon) from the lower layer, a negative bias voltage is applied to the upper electrode 7. When the thickness of the I layer is about 1 μm, the applied bias voltage is about −5 to −10V. When the semiconductor layer 6 is not irradiated with light in such a state, only a current of several to several + pA / mm ² or less flows. On the other hand, when the semiconductor layer 6 is irradiated with light (100 μW / cm ² ) in such a state, a bright current of about 0.3 μA / mm ² is generated. The generated charges are collected by the lower electrode 14. The lower electrode 14 is connected to the drain electrode 13 of the TFT switch 4, and the source electrode 9 of the TFT switch 4 is connected to the signal wiring 3. At the time of image detection, a negative bias is applied to the gate electrode 2 of the TFT switch 4 and held in the off state, and the collected charges are accumulated in the lower electrode 14.

  At the time of image reading, an ON signal (+10 to 20 V) is sequentially applied to the gate electrode 2 of the TFT switch 4 through the scanning wiring 101. As a result, when the TFT switch 4 is sequentially turned on, an electric signal corresponding to the amount of charge accumulated in the lower electrode 14 flows out to the signal wiring 3. The signal detection circuit 105 detects the amount of electric charge accumulated in each sensor unit 103 based on the electric signal flowing out to the signal wiring 3 as information of each pixel constituting the image. Thereby, the image information which shows the image shown with the X-ray irradiated to 10 A of radiation detectors can be obtained.

  By the way, in the radiation detector 10A according to the present embodiment, the common electrode wiring 25 is formed on the non-irradiation surface side of the visible light from the scintillator 30 (downstream side of the visible light) with respect to the sensor unit 103. A bias voltage is supplied to the upper electrode 7 through 22A and 22B. As a result, the light that is converted into visible light by the scintillator 30 and irradiated on the semiconductor layer 6 is not blocked by the common electrode wiring 25, thereby preventing a decrease in light use efficiency in the sensor unit 103. it can.

  Further, in the radiation detector 10A according to the present exemplary embodiment, each photosensor (radiation dose detection sensor) of the AEC photosensor array substrate 74 receives light and detects the radiation dose (total dose). Then, irradiation of radiation by the radiation source is controlled.

  The radiation image detection apparatus 100 provided with the radiation detector 10A of the present embodiment has been described above. 10 A of radiation detectors of this Embodiment have the 2nd surface 1B different from the scintillator 70 which converts the irradiated radiation into light, and the 1st surface 1A and the 1st surface 1A, and the scintillator 70 A plurality of radiation detection pixels each having a switching element for accumulating charges generated by irradiation of the converted light and reading the accumulated charges are provided in a matrix on the first surface 1A side. A plurality of scanning wires 101 through which control signals for switching each switch element provided in the radiation detection pixel flow and a plurality of electrical signals through which electric signals corresponding to the charges accumulated in the radiation detection pixel flow according to the switching state of each switch element. The signal wiring 3 is provided on the first surface side of the TFT array substrate 72 with a photo sensor, and the second surface of the TFT array substrate 72 with a photo sensor. AEC photo provided with a plurality of radiation dose detection sensors provided on the B side and generating charges when irradiated with the light emitted from the second surface 1B by being irradiated on the first surface 1A side And a sensor array substrate 74.

  According to the radiation detector 10A of the present embodiment, since the radiation detection pixel and the radiation irradiation amount detection sensor are provided on different substrates, the yield of the radiation detection pixel and the radiation irradiation amount detection are reduced. The sensor yield can be separated. For example, even when a manufacturing defect occurs in the radiation dose detection sensor, only the AEC photosensor array substrate 74 becomes a defective product. Will not be defective. That is, even if a manufacturing defect occurs in the radiation dose detection sensor, the TFT array substrate 72 with a photosensor in which a plurality of radiation detection pixels are provided in a matrix can be dispensed with. .

  Therefore, according to the present embodiment, it is possible to reduce the manufacturing cost as compared with the prior art.

  Further, according to the present embodiment, since no radiation irradiation amount detection sensor is provided between the radiation detection pixels, an AEC sensor (first element) is provided in the gap between the first radiation conversion elements (elements for radiation detection). Compared with the prior art in which the second radiation conversion element) is formed, the effective detection area of the radiation detection pixel can be enlarged, and the accuracy of radiation detection is improved.

  The AEC photosensor array substrate 74 in which a plurality of radiation dose detection sensors are arranged is provided on the second surface side of the photosensor-equipped TFT array substrate 72 in which a plurality of radiation detection pixels are provided in a matrix. Therefore, for example, more radiation (for example, light) of the second wavelength can be received than when the AEC sensor is formed in the gap between the radiation detection TFTs, and the detection sensitivity becomes higher. This is because when the AEC sensor is formed in the gap of the TFT, the sensor part of the AEC sensor having a smaller area than the gap provided with the AEC sensor receives the radiation of the second wavelength. In this embodiment, since the AEC sensor is arranged on the upper surface of the TFT, the AEC sensor can be arranged in the entire gap of the TFT, and more radiation of the second wavelength leaked from the gap can be received. Because.

Further, since the light converted by the same scintillator 70 (wavelength conversion unit) is detected by the radiation detection pixel and the radiation irradiation amount detection sensor, the irradiation is performed as compared with the case where the irradiation amount is detected by the external AEC sensor. Deviation between image detection and radiation dose detection according to conditions can be reduced.
[Second Embodiment]
Next, a second embodiment will be described. In addition, the same code | symbol is attached | subjected about the thing similar to 1st Embodiment. Similarly to the first embodiment, in the following description, radiation having the first wavelength is simply referred to as “radiation (for example, X-ray)”, and radiation having a second wavelength different from the first wavelength. However, the radiation of the first wavelength and the radiation of the second wavelength are not limited to this. As shown in FIG. 10, the radiation detector 10 </ b> B of the second embodiment includes a scintillator 70 ′, a photosensor-equipped TFT array substrate 72, and an AEC photosensor array substrate 74.

  The scintillator 70 'according to the present embodiment emits light from both sides by removing the reflector provided in the scintillator 70 according to the first embodiment. That is, the scintillator 70 ′ of the present embodiment converts irradiated radiation into light and irradiates light from both sides. Note that the scintillator 70 ′ of the present embodiment corresponds to the wavelength conversion unit (wavelength conversion layer) of the present invention.

  In the present embodiment, the TFT array substrate 72 with photosensor is provided on one surface side of the scintillator 70 ′, and light emitted from the one surface is irradiated onto the TFT array substrate 72 with photosensor. It has come to be. Thus, each of the plurality of radiation detection pixels provided on the photosensor-equipped TFT array substrate 72 accumulates electric charges generated by irradiation with light emitted from the one surface. Note that the radiation detection pixel according to the present embodiment includes a switch element for reading out the accumulated charges, as in the first embodiment.

  In this embodiment, the AEC photosensor array substrate 74 is provided on the other surface side of the scintillator 70 ′, and light emitted from the other surface is irradiated onto the AEC photosensor array substrate 74. It has come to be. As a result, each of the plurality of photosensors (radiation dose detection sensors) provided on the AEC photosensor array substrate 74 generates an electric charge when irradiated with the light emitted from the other surface.

  By designing in this way, the radiation irradiation amount detection sensor of the first embodiment receives only light leaking from the gap between the TFT array substrate 72 with a photosensor, but the radiation irradiation of the present embodiment. Since the quantity detection sensor can receive all the light emitted from the other surface, the detection sensitivity is increased.

  Next, the manufacturing method of the radiographic image detection apparatus of this Embodiment is demonstrated. FIG. 11 shows an outline of a method for manufacturing the radiological image detection apparatus of the present embodiment. FIG. 12 shows a cross-sectional view of an object manufactured at each stage of the manufacturing method.

  First, a TFT array substrate 72 with a photosensor is manufactured, and a shipping inspection of the manufactured TFT array substrate 72 with a photosensor is performed (see FIGS. 11A and 12A).

  Next, the scintillator 70 'is bonded to the TFT array substrate 72 with a photosensor determined to be a non-defective product (not a defective product) by a shipping inspection using an adhesive as described above (FIG. 11B). And FIG. 12B).

  Further, the AEC photosensor array substrate 74 is manufactured, and the manufactured AEC photosensor array substrate 74 is inspected for shipment (see FIGS. 11C and 12C).

  Then, the AEC photosensor array substrate 74 determined to be a non-defective product (not a defective product) in the shipping inspection is applied to the scintillator 70 ′ with the photosensor-attached TFT array substrate 72 bonded thereto, as described above. (See FIGS. 11D and 12D.)

  Then, secondary division is performed to electrically and physically separate each terminal, and a gate driver and an amplifier IC are mounted (TCP mounting: mounting an IC mounted in a tape carrier package), and finally a circuit board ( A gate drive board, a signal detection circuit board, etc.) are mounted, and the radiation detector 10B of the radiation image detection apparatus is completed (see FIG. 11E).

  In the present embodiment, the photosensor-equipped TFT array substrate 72 shown in FIG. 9A and the AEC photosensor array substrate 74 shown in FIG. As shown in FIG. 13B, the scintillators 70 'are arranged above and below the single scintillator 70'.

  Next, the operation principle of the radiation image detection apparatus having the above structure according to the present embodiment will be described.

When X-rays are irradiated from above in FIG. 10, the irradiated X-rays are absorbed by the scintillator 70 ′ and converted into visible light (radiation having the second wavelength). Note that X-rays may be irradiated from below in FIG. 10. In this case as well, the irradiated X-rays are absorbed by the scintillator 70 'and converted into visible light. The amount of light generated from the scintillator 70 ′ is 0.5 to ² μW / cm ² in normal X-ray imaging for medical diagnosis. This generated light is irradiated from both sides of the scintillator 70 '. The generated light (light irradiated from one surface of the scintillator 70 ′) passes through the adhesive resin 28 layer and irradiates the semiconductor layer 6 of the sensor unit 103 arranged in an array on the TFT array substrate. Is done. The generated light (light irradiated from the other surface of the scintillator 70 ′) reaches the AEC photosensor array substrate 74, and the AEC photosensor array substrate 74 receives a part of the generated light. .

In the radiation detector 10B, the semiconductor layer 6 is provided separately for each pixel unit. A predetermined bias voltage is applied to the semiconductor layer 6 from the upper electrode 7 through the common electrode wiring 25, and when light is irradiated, charges are generated inside. For example, in the case of a PIN structure in which the semiconductor layer 6 is laminated in the order of n ⁺ -ip ⁺ (n ⁺ amorphous silicon, amorphous silicon, p ⁺ amorphous silicon) from the lower layer, a negative bias voltage is applied to the upper electrode 7. When the thickness of the I layer is about 1 μm, the applied bias voltage is about −5 to −10V. When the semiconductor layer 6 is not irradiated with light in such a state, only a current of several to several + pA / mm ² or less flows. On the other hand, when the semiconductor layer 6 is irradiated with light (100 μW / cm ² ) in such a state, a bright current of about 0.3 μA / mm ² is generated. The generated charges are collected by the lower electrode 14. The lower electrode 14 is connected to the drain electrode 13 of the TFT switch 4, and the source electrode 9 of the TFT switch 4 is connected to the signal wiring 3. At the time of image detection, a negative bias is applied to the gate electrode 2 of the TFT switch 4 and held in the off state, and the collected charges are accumulated in the lower electrode 14.

  At the time of image reading, an ON signal (+10 to 20 V) is sequentially applied to the gate electrode 2 of the TFT switch 4 through the scanning wiring 101. As a result, when the TFT switch 4 is sequentially turned on, an electric signal corresponding to the amount of charge accumulated in the lower electrode 14 flows out to the signal wiring 3. The signal detection circuit 105 detects the amount of electric charge accumulated in each sensor unit 103 based on the electric signal flowing out to the signal wiring 3 as information of each pixel constituting the image. Thereby, the image information which shows the image shown with the X-ray irradiated to the radiation detector 10B can be obtained.

  In the radiation detector 10B according to the present exemplary embodiment, each photosensor (radiation dose detection sensor) of the AEC photosensor array substrate 74 receives light, and a radiation dose (total dose) is detected. The irradiation of radiation by the radiation source is controlled.

  The radiation image detection apparatus provided with the radiation detector 10B of the present embodiment has been described above. The radiation detector 10B according to the present embodiment is provided on one surface side of the scintillator 70 ′ and the scintillator 70 ′ that converts the irradiated radiation into light and emits light from both surfaces, and one of the scintillators 70 ′. A plurality of radiation detection pixels each having a switch element for accumulating charges generated by irradiating light emitted from the surface and reading the accumulated charges are provided in a matrix, and each radiation detection pixel A plurality of scanning wirings 101 through which control signals for switching the respective switch elements are provided, and a plurality of signal wirings 3 through which electric signals according to the electric charges accumulated in the radiation detection pixels flow according to the switching state of each switch element; Is provided on the other surface side of the scintillator 70 ′, and the other side of the scintillator 70 ′. And an AEC photosensor array substrate 74 provided with a plurality of radiation dose detection sensors that generate charges when irradiated with light emitted from the other surface.

  According to the radiation detector 10B of the present embodiment, since the radiation detection pixel and the radiation irradiation amount detection sensor are provided on different substrates, the yield of the radiation detection pixel and the radiation irradiation amount detection are reduced. The sensor yield can be separated. For example, even when a manufacturing defect occurs in the radiation dose detection sensor, only the AEC photosensor array substrate 74 becomes a defective product. Will not be defective. That is, even if a manufacturing defect occurs in the radiation dose detection sensor, the TFT array substrate 72 with a photosensor in which a plurality of radiation detection pixels are provided in a matrix can be dispensed with. .

  Therefore, according to the present embodiment, it is possible to reduce the manufacturing cost as compared with the prior art.

  Further, according to the present embodiment, since no radiation irradiation amount detection sensor is provided between the radiation detection pixels, an AEC sensor (first element) is provided in the gap between the first radiation conversion elements (elements for radiation detection). Compared with the prior art in which the second radiation conversion element) is formed, the effective detection area of the radiation detection pixel can be enlarged, and the accuracy of radiation detection is improved.

  Further, since the AEC photosensor array substrate 74 on which a plurality of radiation dose detection sensors are arranged is provided on the other surface side of the scintillator 70 ′, for example, the AEC sensor is placed in the gap between the radiation detection TFTs. More radiation of the second wavelength (for example, light) can be received than when formed, and the detection sensitivity becomes higher. This is because when the AEC sensor is formed in the gap of the TFT, the sensor part of the AEC sensor having a smaller area than the gap provided with the AEC sensor receives the radiation of the second wavelength. In the present embodiment, since the AEC sensor on the upper surface of the TFT is arranged, the AEC sensor can be arranged in the entire gap of the TFT. For example, the second wavelength of the second wavelength converted by the scintillator 70 'and emitted from the other surface. This is because more radiation can be received. Note that the detection sensitivity is higher than that of the first embodiment because the amount of light received by this embodiment is larger than that of the first embodiment.

  In addition, since the light converted by the same scintillator 70 '(wavelength conversion unit) is detected by the radiation detection pixel and the radiation dose detection sensor, compared with the case where the dose detection is performed by the external AEC sensor, Deviation between image detection and radiation dose detection according to irradiation conditions can be reduced.

  Further, according to this embodiment, there is no radiation absorption loss due to the AEC photosensor array substrate 74, and the image quality is improved. Further, according to the present embodiment, the AEC photosensor array substrate 74 is provided on the non-radiation side opposite to the side irradiated with radiation. As described above, the AEC photosensor array substrate 74 is converted by the same scintillator 70 '. Since the emitted light is detected by the radiation detection pixel and the radiation dose detection sensor, it is possible to suppress deterioration in the accuracy of radiation dose detection due to radiation absorption by the photosensor-equipped TFT array substrate 72.

  In addition, the configuration of the radiographic imaging device 100 described in the first embodiment and the configuration of the radiation detection element 10A, and the configuration of the radiographic imaging device described in the second embodiment, and the radiation detection It goes without saying that the configuration of the element 10B is an example, and can be changed as appropriate without departing from the gist of the present invention.

  For example, in the first embodiment and the second embodiment, a radiation irradiation amount detection sensor may be provided on the entire surface of the AEC photosensor array substrate 74, and a part of the AEC photoarray substrate 44 may be provided. A radiation irradiation amount detection sensor may be provided.

3 Signal wiring 4 TFT switch 10A Radiation detector 70 Scintillator 72 TFT array substrate with photo sensor 74 Photo sensor array substrate for AEC 100 Radiation imaging device

Claims (10)

A scintillator that converts the irradiated radiation of the first wavelength into visible light having a longer wavelength than the first wavelength;
A first surface that is a radiation incident side and a second surface that is different from the first surface are irradiated with the visible light from the scintillator provided on the first surface side. A plurality of radiation detection pixels each having a switch element for accumulating the generated charges and reading the accumulated charges are provided in a matrix on the first surface side, and each radiation detection pixel is provided. A plurality of scanning wirings through which control signals for switching each switch element flow and a plurality of signal wirings through which an electrical signal corresponding to the charge accumulated in the radiation detection pixel flows according to the switching state of each switch element. A first substrate provided on the first surface side;
A plurality of the first substrate is provided on the second surface side, and generates a charge by irradiating the visible light emitted from the second surface by irradiating the first surface. A second substrate on which a radiation dose detection sensor is provided in a matrix,
The plurality of radiation dose detection sensors provided in a matrix are provided on the entire surface of the second substrate, and each of the plurality of radiation dose detection sensors is connected to each of the radiation dose detection wirings. And
An electrical signal corresponding to the charge generated in the connected radiation dose detection sensor flows through each of the radiation dose detection wires, and each of the radiation dose detection wires has the first wavelength. A radiation detector connected to a radiation irradiation control device that detects radiation dose of the first wavelength and controls radiation of the first wavelength by a radiation source that irradiates radiation of the first wavelength based on the radiation dose.   2. The radiation detector according to claim 1, wherein an area of each of the plurality of radiation dose detection sensors is larger than an area of each of the plurality of radiation detection pixels.   3. The radiation according to claim 1, wherein the plurality of radiation detection pixels are provided in a matrix in a region where the plurality of radiation dose detection sensors provided in a matrix are formed. Detector.   The reflector which is a member for reflecting light is provided in the surface on the opposite side to the surface which contact | connects the said 1st surface of the said scintillator. Radiation detector.   The radiation detector according to any one of claims 1 to 4, wherein the second substrate includes a resin substrate.   The radiation detector according to any one of claims 1 to 5, wherein the radiation irradiation amount detection sensor includes an organic material.   The radiation detector according to any one of claims 1 to 5, wherein the radiation irradiation amount detection sensor includes an inorganic material.   The radiation detector according to any one of claims 1 to 7, wherein the scintillator includes GOS.   The radiation detector according to any one of claims 1 to 7, wherein the scintillator includes CsI. A scintillator that converts the irradiated radiation of the first wavelength into visible light having a longer wavelength than the first wavelength;
A first surface that is a radiation incident side and a second surface that is different from the first surface are irradiated with the visible light from the scintillator provided on the first surface side. A plurality of radiation detection pixels each having a switch element for accumulating the generated charges and reading the accumulated charges are provided in a matrix on the first surface side, and each radiation detection pixel is provided. A plurality of scanning wirings through which a control signal for switching each of the switching elements flows, and a plurality of signal wirings through which an electric signal corresponding to the charge accumulated in the radiation detection pixel flows according to the switching state of each switching element. A first substrate provided on the first surface side;
A plurality of the first substrate is provided on the second surface side, and generates a charge by irradiating the visible light emitted from the second surface by irradiating the first surface. A second substrate on which a radiation dose detection sensor is provided in a matrix,
The plurality of radiation dose detection sensors provided in a matrix are provided on the entire surface of the second substrate, and each of the plurality of radiation dose detection sensors is connected to each of the radiation dose detection wirings. And
An electrical signal corresponding to the charge generated in the connected radiation dose detection sensor flows through each of the radiation dose detection wires, and each of the radiation dose detection wires has the first wavelength. A radiation detector connected to a radiation irradiation control device that detects radiation dose of the first wavelength and controls radiation of the first wavelength radiation by a radiation source that irradiates the radiation of the first wavelength based on the radiation dose; ,
A radiation source for injecting radiation from the first surface side of the first substrate;
A radiographic imaging apparatus comprising: