WO2013065682A1

WO2013065682A1 - Radiological imaging device, radiological image processing device, radiological imaging system, radiological imaging method, and radiological imaging program

Info

Publication number: WO2013065682A1
Application number: PCT/JP2012/078035
Authority: WO
Inventors: 大田　恭義; 西納　直行; 中津川　晴康; 岩切　直人; 北野　浩一
Original assignee: 富士フイルム株式会社
Priority date: 2011-10-31
Filing date: 2012-10-30
Publication date: 2013-05-10

Abstract

The present invention is capable of improving the quality of radiological images. Specifically, an electronic cassette: has a radiation detector provided with two panels; generates first image information corresponding to charges read by a panel positioned on the side on which radiation (X) is emitted, and generates second image information corresponding to charges read by a panel positioned on the side on which the radiation (X) is not emitted; generates composite image information, which is obtained by synthesizing first image information and second image information for which charges accumulated at the same time or can be regarded as having accumulated at the same time, according to a composition ratio corresponding to conditions; and sends the composite image information to a radiological image processing device. In the radiological image processing device, composite images corresponding to the received composite image information are controlled so as to be displayed on one of two displays.

Description

Radiation image capturing apparatus, radiation image processing apparatus, radiation image capturing system, radiation image capturing method, and radiation image capturing program

The present invention relates to a radiographic image capturing apparatus, a radiographic image processing apparatus, a radiographic image capturing system, a radiographic image capturing method, and a radiographic image capturing program. In particular, the present invention relates to a radiographic imaging apparatus, a radiographic image processing apparatus, a radiographic imaging system, a radiographic imaging method, and a radiographic imaging program including a radiation detector having a plurality of substrates.

As a radiographic imaging apparatus for capturing radiographic images, a radiographic imaging apparatus that detects radiation irradiated from a radiation irradiation apparatus and transmitted through a subject with a radiation detector is known. In addition to capturing a radiographic image that is a still image, the radiographic image capturing apparatus captures a moving image that continuously captures a plurality of radiographic images (still images), for example.

In such a radiation detector, there is a technique for simultaneously capturing two radiation images. For example, as described in Japanese Patent Application Laid-Open No. 2001-22015, each of the stimulated emission light emitted from both sides of the stimulable phosphor sheet on which radiation image information is accumulated and recorded by the irradiation of excitation light is detected. There is known a double-sided condensing type radiological image information reading device that adds and outputs two image signals carrying the radiographic image information obtained by the above-mentioned method. Further, as described in Japanese Patent Application Laid-Open No. 2010-056397, by providing a radiation detection unit for detecting the irradiated radiation and generating the charge on both surfaces of the substrate for reading out the charge, A technique for obtaining a plurality of radiographic images by radiations having different energies by irradiation is known.

The above-described technique is a calculation process (so-called subtraction image processing) for calculating a difference by applying a weight to a radiographic image obtained by radiography, in particular, an image part corresponding to a hard part element such as a bone part in the image, and a soft part The image quality of a radiographic image can be improved by using it when obtaining a radiographic image (so-called energy subtraction image) in which one of image portions corresponding to a tissue or the like is emphasized and the other is removed.

However, in the case of performing imaging using a technique capable of simultaneously obtaining a plurality of radiation images with one radiation image capturing apparatus in this way, a plurality of radiation images are added to generate one radiation image. In addition, there is a concern that the image quality of the radiographic image is degraded. For example, in the case where a plurality of radiation detection units (for example, scintillators) are provided, image blur may be caused if their characteristics are different. In addition, image blur may be caused by the radiation dose (energy).

The present invention provides a radiographic image capturing apparatus, a radiographic image processing apparatus, a radiographic image capturing system, a radiographic image capturing method, and a radiographic image capturing program capable of improving the image quality of a radiographic image.

A first aspect of the present invention is a radiographic imaging system, a radiation conversion unit that converts radiation into at least one of electric charge and fluorescence according to the irradiated radiation, and electric charges converted and accumulated by the radiation conversion unit Of the first charge detection unit connected to the radiation conversion unit for detecting the fluorescence or the second charge detection unit connected to the radiation conversion unit for detecting the accumulated charge by converting the fluorescence converted by the radiation conversion unit A radiation detector comprising a first substrate comprising either, a second substrate comprising either the first charge detector or the second charge detector, and a first based on the charge detected by the first substrate. A generating unit that generates image information and generates second image information based on the electric charge detected by the second substrate, and one of the first image information and the second image information generated by the generating unit. Combining information with the other image information generated based on the charge accumulated at a predetermined timing that is regarded as the same timing as the charge accumulation timing when one image information is generated by the generating means Combining means for generating image information, and transmitting means for transmitting the composite image information synthesized by the synthesizing means to the outside.

The radiation detector of the present invention includes a radiation conversion unit, a first substrate, and a second substrate. The radiation conversion unit converts the radiation into at least one of electric charge and fluorescence according to the irradiated radiation. The first substrate converts charges accumulated by converting the fluorescence converted by the first charge detection unit or the radiation conversion unit connected to the radiation conversion unit for detecting the charges converted and accumulated by the radiation conversion unit. One of the second charge detection units connected to the radiation conversion unit to be detected is provided. The second substrate includes either the first charge detection unit or the second charge detection unit.

The generating unit generates the first image information based on the electric charge detected by the first substrate, and generates the second image information based on the electric charge detected by the second substrate.

In this way, two images (first image information and second image information) are photographed using one radiation detector, and the two photographed images are combined to form one image (synthesized image) as display means. In the case of displaying, if the first image information and the second image information are simply combined, the image quality of the combined image may deteriorate. For example, there is a concern that the image quality deteriorates when the characteristics of the first substrate and the second substrate are different or according to the dose (energy) of the irradiated radiation.

Therefore, the synthesizing unit has one image information of the first image information and the second image information generated by the generating unit, and the same timing as the charge accumulation timing when the one image information is generated by the generating unit. Composite image information is generated by combining the other image information generated based on the charge accumulated at a predetermined timing to be considered. The transmission means transmits the composite image information synthesized by the synthesis means to the outside.

Thus, the image quality of the radiation image can be improved by combining the first image information and the second image information.

According to a second aspect of the present invention, in the first aspect, it is preferable that the synthesizing unit synthesizes at a synthesis ratio corresponding to at least one of a pre-registered shooting condition and a condition predetermined by the user.

According to a third aspect of the present invention, in the above aspect, when the moving image is shot, the generating unit generates the first image information and the second image information at a predetermined frame rate according to the moving image shooting. It is preferable to do.

According to a fourth aspect of the present invention, in the third aspect, when the predetermined frame rates of the first image information and the second image information are different, either one of the predetermined frame rates is set. It is preferable that an interpolation unit for generating an interpolated image is provided so that the synthesizing unit generates the synthesized image information using the interpolated image information.

Further, in a fifth aspect of the present invention based on the above aspect, the transmitting means may transmit a composite ratio when the composite image information is combined together with the composite image information.

Further, in a sixth aspect of the present invention based on the above aspect, the transmission means may transmit the first image information and the second image information through different paths.

Further, according to a seventh aspect of the present invention, in the above aspect, the radiation conversion unit includes a first radiation conversion layer stacked on the first substrate and a sensitivity to the radiation stacked on the second substrate. And a second radiation conversion layer different from the above.

Further, an eighth aspect of the present invention is the seventh aspect, wherein the first radiation conversion layer is a direct conversion type that converts radiation into electric charge, and is provided on the radiation irradiation side of the second radiation conversion layer. It is preferable that
According to a ninth aspect of the present invention, in the seventh aspect or the eighth aspect, the first radiation conversion layer is more sensitive to a low energy component of radiation than the second radiation conversion layer. It is preferable that the second radiation conversion layer is provided on the radiation irradiation side.

According to a tenth aspect of the present invention, the predetermined timing of the radiographic image capturing apparatus according to any one of the first to ninth aspects is determined when one image information is generated by the generation unit. At least one of the timing at which at least a part of the charge accumulation period overlaps the charge accumulation period and the timing within a predetermined range from the charge accumulation timing when one image information is generated by the generating means It is preferable that
11th aspect of this invention is a radiographic image processing apparatus, Comprising: Reception which receives the synthetic image information transmitted from the radiographic imaging apparatus which is any one aspect of the said 10th aspect from the said 1st aspect It is preferable to include a control unit that controls the display unit to display a composite image corresponding to the composite image information received by the reception unit.

Also, in a twelfth aspect of the present invention, in the eleventh aspect, the control means preferably controls the display means to display a composite ratio image indicating a composite ratio of the composite image.

Further, a thirteenth aspect of the present invention is the radiographic imaging device according to the eleventh aspect or the twelfth aspect, wherein the radiographic imaging apparatus receives the setting means for receiving the composite image composition ratio and the composite ratio received by the reception means. It is preferable to include a composition ratio transmission means for transmitting.

A fourteenth aspect of the present invention is a radiographic image capturing system, wherein the radiographic image capturing apparatus according to any one of the first aspect to the tenth aspect and composite image information from the radiographic image capturing apparatus. The radiographic image processing apparatus according to any one of the eleventh aspect to the thirteenth aspect is provided.

According to a fifteenth aspect of the present invention, in the fourteenth aspect, a predetermined frame rate of the first image information and the second image information generated by the radiation irradiation apparatus and the generation unit of the radiographic image capturing apparatus. Is different, it is preferable to include a radiation irradiation control means for controlling the radiation irradiation apparatus so that the radiation detector is continuously irradiated with radiation during the period of moving image shooting.

According to a sixteenth aspect of the present invention, there is provided a radiographic imaging method, a radiation conversion unit that converts radiation into at least one of charge and fluorescence according to the irradiated radiation, and the charge converted and accumulated by the radiation conversion unit. Of the first charge detection unit connected to the radiation conversion unit for detecting the fluorescence of the two charge detection unit connected to the radiation conversion unit for detecting the accumulated charge by converting the fluorescence converted by the radiation conversion unit Based on the charge detected by the first substrate using a radiation detector comprising a first substrate comprising any one, a second substrate comprising either the first charge detector or the second charge detector. One of the generation step of generating the first image information and generating the second image information based on the electric charge detected by the second substrate, and the first image information and the second image information generated by the generation step The image information is combined with the other image information generated based on the charge accumulated at a predetermined timing that is regarded as the same timing as the charge accumulation timing when one image information is generated in the generation process. The image forming apparatus includes a combining step of generating combined image information and a transmitting step of transmitting the combined image information combined by the combining step to the outside.

A seventeenth aspect of the present invention is a radiographic imaging program, a radiation conversion unit that converts radiation into at least one of charge and fluorescence in accordance with the irradiated radiation, and the charge converted and accumulated by the radiation conversion unit Of the first charge detection unit connected to the radiation conversion unit for detecting the fluorescence or the second charge detection unit connected to the radiation conversion unit for detecting the accumulated charge by converting the fluorescence converted by the radiation conversion unit A radiation detector comprising a first substrate comprising either, a second substrate comprising either the first charge detector or the second charge detector, and a first based on the charge detected by the first substrate. A generating unit that generates image information and generates second image information based on the electric charge detected by the second substrate, and one of the first image information and the second image information generated by the generating unit The image information is combined with the other image information generated based on the charge accumulated at a predetermined timing that is regarded as the same timing as the charge accumulation timing when one image information is generated by the generating means. An apparatus for causing a computer to function as a generating unit and a synthesizing unit of a radiographic image capturing apparatus including a synthesizing unit that generates synthetic image information and a transmission unit that transmits the synthesized image information synthesized by the synthesizing unit It is.

According to the above aspect of the present invention, the image quality of the radiation image can be improved.

1 is a schematic configuration diagram of an outline of an overall configuration of an example of a radiographic imaging system according to the present embodiment. It is a cross-sectional schematic diagram which shows an example of a structure of the radiation detector which concerns on this Embodiment. It is the schematic of a cross section which shows an example of a structure of the radiation detector which concerns on this Embodiment. It is explanatory drawing for demonstrating the columnar crystal structure of the indirect conversion type radiation conversion layer of the radiation detector which concerns on this Embodiment. The other example of the structure of the radiation detector which concerns on this Embodiment is shown, and the cross section by which the radiation conversion layer, the panel 1, the panel 2, and the radiation conversion layer were laminated | stacked in order from the side irradiated with the radiation X is shown. It is a schematic diagram. The other example of the structure of the radiation detector which concerns on this Embodiment is shown, and it is the cross section by which the panel 1, the radiation conversion layer, the panel 2, and the radiation conversion layer were laminated | stacked in order from the radiation X irradiation side. It is a schematic diagram. The other example of the structure of the radiation detector which concerns on this Embodiment is shown, and it is the cross section by which the radiation conversion layer, the panel 1, the radiation conversion layer, and the panel 2 were laminated | stacked in order from the radiation X irradiation side. It is a schematic diagram. The other example of the structure of the radiation detector which concerns on this Embodiment is shown, and it is a schematic diagram of the cross section provided with two indirect conversion type radiation conversion layers. The other example of the structure of the radiation detector which concerns on this Embodiment is shown, and it is a schematic diagram of the cross section provided with two direct conversion type radiation conversion layers. The other example of the structure of the radiation detector which concerns on this Embodiment is shown, and it is a schematic diagram of the cross section provided with one direct conversion type radiation conversion layer. The other example of the structure of the radiation detector which concerns on this Embodiment is shown, and it is a schematic diagram of the cross section provided with one indirect conversion type radiation conversion layer. The schematic circuit block diagram of an example of the electronic cassette concerning this Embodiment is shown. It is a functional block diagram for demonstrating an example of the function of the electronic cassette concerning this Embodiment. It is explanatory drawing for demonstrating the characteristic of the radiation detector which concerns on this Embodiment, and is explanatory drawing which showed typically the case where the radiation X irradiated is a low energy. It is explanatory drawing for demonstrating the characteristic of the radiation detector which concerns on this Embodiment, and is explanatory drawing which showed typically the case where the radiation X irradiated is high energy. It is explanatory drawing for demonstrating the characteristic of the radiation detector which concerns on this Embodiment. It is a functional block diagram for demonstrating an example of the radiographic image processing function of the radiographic image processing apparatus which concerns on this Embodiment. It is explanatory drawing which shows a specific example of the display state of the display which concerns on this Embodiment. It is a flowchart which shows an example of the radiographic imaging process of the radiographic imaging system which concerns on this Embodiment. It is a flowchart which shows an example of the synthetic | combination image generation process of the radiographic image process which concerns on this Embodiment. It is explanatory drawing for demonstrating a specific example of the frame rate of an electronic cassette provided with the radiation detector shown to FIG. 2A and FIG. 2B, and has shown the case where a radiation is irradiated continuously. It is a flowchart which shows an example of the radiographic image process of the radiographic imaging system which concerns on this Embodiment. It is explanatory drawing for demonstrating the intermittent irradiation (pulse irradiation) of a radiation in the case where a frame rate differs in the electronic cassette provided with the radiation detector shown to FIG. 2A and 2B.

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

First, a schematic configuration of the entire radiographic imaging system including the radiographic image processing apparatus of the present embodiment will be described. FIG. 1 shows a schematic configuration diagram of an overall configuration of an example of a radiographic imaging system according to the present exemplary embodiment. The radiographic image capturing system 10 of the present embodiment can capture still images in addition to radiographic images as moving images. Note that in this embodiment, a moving image refers to displaying still images one after another at a high speed and recognizing them as moving images. The still images are captured, converted into electric signals, transmitted, and transmitted. The process of replaying a still image is repeated at high speed. Accordingly, the moving image includes so-called “frame advance” in which the same area (part or all) is photographed a plurality of times within a predetermined time and continuously reproduced according to the degree of “high speed”. Shall be.

The radiographic imaging system 10 of the present exemplary embodiment is based on an instruction (imaging menu) input from an external system (for example, RIS: Radiology Information System: radiation information system) via the console 16. It has a function of taking a radiographic image by an operation such as the above.

Further, the radiographic image capturing system 10 of the present embodiment displays a moving image and a still image of the captured radiographic image on the display 50 of the console 16 and the radiographic image interpretation device 18, thereby allowing a doctor, a radiographer, or the like to perform radiation. It has a function to interpret images.

The radiographic imaging system 10 according to the present exemplary embodiment includes a radiation generation device 12, a radiographic image processing device 14, a console 16, a storage unit 17, a radiographic image interpretation device 18, and an electronic cassette 20.

The radiation generator 12 includes a radiation irradiation control unit 22. The radiation irradiation control unit 22 has a function of irradiating the imaging target region of the subject 30 on the imaging table 32 with the radiation X from the radiation irradiation source 22 </ b> A based on the control of the radiation control unit 62 of the radiation image processing apparatus 14. ing.

The radiation X transmitted through the subject 30 is applied to the electronic cassette 20 held in the holding unit 34 inside the imaging table 32. The electronic cassette 20 generates charges according to the dose of the radiation X that has passed through the subject 30, and based on the generated charge amount, image data indicating a radiation image (first image and second image, details will be described later). It has a function to generate and output. The electronic cassette 20 of this embodiment includes a radiation detector 26. The radiation detector 26 of the present embodiment includes two panels (panel 1 and panel 2) (details will be described later).

In the present embodiment, image information indicating a radiographic image output from the electronic cassette 20 is input to the console 16 via the radiographic image processing device 14. The console 16 according to the present embodiment uses the radiography (LAN: Local Area Network) or the like from an external system (RIS) or the like, using a radiographing menu, various types of information, or the like. It has a function to perform control. In addition, the console 16 according to the present embodiment has a function of transmitting / receiving various types of information including image data of radiographic images to / from the radiographic image processing apparatus 14 and a function of transmitting / receiving various types of information to / from the electronic cassette 20. have.

The console 16 in the present embodiment is a server computer. The console 16 includes a control unit 40, a display driver 48, a display 50, an operation input detection unit 52, an operation panel 54, an I / O unit 56, and an I / F unit 58.

The control unit 40 has a function of controlling the operation of the entire console 16, and includes a CPU, a ROM, a RAM, and an HDD. The CPU has a function of controlling the operation of the entire console 16. Various programs including a control program used by the CPU are stored in advance in the ROM. The RAM has a function of temporarily storing various data. An HDD (Hard Disk Drive) has a function of storing and holding various data.

The display driver 48 has a function of controlling display of various information on the display 50. The display 50 according to the present embodiment has a function of displaying an imaging menu, a captured radiographic image, and the like. The display 50 is a touch panel (operation panel 54). The operation input detection unit 52 has a function of detecting an operation state with respect to the operation panel 54. The operation panel 54 is used for inputting various kinds of information and operation instructions by a doctor or a radiographer who is a radiographer who takes a radiographic image, and a doctor or radiographer who is an interpreter who interprets the radiographic image taken. belongs to. The operation panel 54 of the present embodiment includes at least a touch panel. Note that the operation panel 54 of the present embodiment includes a touch pen, a plurality of keys, a mouse, and the like.

The I / O unit 56 and the I / F unit 58 transmit and receive various types of information to and from the radiographic image processing apparatus 14 and the radiation generating apparatus 12 through wireless communication, and image data to and from the electronic cassette 20. And the like.

The control unit 40, the display driver 48, the operation input detection unit 52, and the I / O unit 56 are connected to each other via a bus 59 such as a system bus or a control bus so that information can be exchanged. Therefore, the control unit 40 controls the display of various information on the display 50 via the display driver 48 and controls the transmission / reception of various information with the radiation generator 12 and the electronic cassette 20 via the I / F unit 58. Each can be done. Further, the control unit 40 can grasp the operation state (instruction input) of the image interpreter with respect to the operation panel 54 via the operation input detection unit 52.

The radiation image processing apparatus 14 according to the present embodiment has a function of controlling the radiation generation apparatus 12 and the electronic cassette 20 based on an instruction from the console 16. The radiographic image processing device 14 has a function of controlling the display of the radiographic image (composite image) received from the electronic cassette 20 on the display 50 of the console 16 and the radiographic image interpretation device 18 (details will be described later).

The radiation image processing apparatus 14 according to the present embodiment includes a system control unit 60, a radiation control unit 62, a panel control unit 64, an image processing control unit 66, and an I / F unit 68.

The system control unit 60 has a function of controlling the entire radiographic image processing apparatus 14 and a function of controlling the radiographic image capturing system 10. The system control unit 60 includes a CPU, ROM, RAM, and HDD. The CPU has a function of controlling operations of the entire radiographic image processing apparatus 14 and the radiographic image capturing system 10. Various programs including a control program used by the CPU are stored in advance in the ROM. The RAM has a function of temporarily storing various data. An HDD (Hard Disk Drive) has a function of storing and holding various data. The radiation control unit 62 has a function of controlling the radiation irradiation control unit 22 of the radiation generator 12 based on an instruction from the console 16. The panel control unit 64 has a function of receiving information from the electronic cassette 20 wirelessly or by wire. The image processing control unit 66 has a function of performing various image processing on the radiation image.

The system control unit 60, the radiation control unit 62, the panel control unit 64, and the image processing control unit 66 are connected to each other through a bus 69 such as a system bus or a control bus so as to be able to exchange information.

The storage unit 17 of the present embodiment has a function of storing captured radiographic images (first image and second image) and information related to the radiographic image. The storage unit 17 is, for example, an HDD.

Further, the radiographic image interpretation apparatus 18 of the present embodiment is an apparatus having a function for an interpreter such as a doctor to interpret a radiographic image taken. Although the radiographic image interpretation apparatus 18 is not specifically limited, What is called an image interpretation viewer, a console, a tablet terminal, etc. are mentioned. The radiographic image interpretation apparatus 18 of the present embodiment is a personal computer. Similar to the console 16 and the radiographic image processing apparatus 14, the radiographic image interpretation apparatus 18 includes a CPU, ROM, RAM, HDD, display driver, display 23, operation input detection unit, operation panel 24, I / O unit, and I / O unit. F section is provided. In FIG. 1, only the display 23 and the operation panel 24 are shown, and other descriptions are omitted in order to avoid complicated description.

Next, the electronic cassette 20 will be described in detail. First, the radiation detector 26 provided in the electronic cassette 20 will be described. The radiation detector 26 of the present embodiment includes two TFT substrates (panels). In the following, a panel having a TFT substrate disposed on the radiation X irradiation side is referred to as a panel 1 and is disposed on the non-irradiation side (the side farther from the surface irradiated with the radiation X than the panel 1). A panel provided with a TFT substrate is referred to as a panel 2.

An example of the radiation detector 26 is shown in FIGS. 2A and 2B. FIG. 2A is a schematic cross-sectional view of an example of the radiation detector 26. FIG. 2B is a schematic cross-sectional view of an example of the radiation detector 26. The radiation detector 26 shown in FIGS. 2A and 2B includes two TFT substrates (panel 1 and panel 2) and two radiation conversion layers. Specifically, the TFT substrate 70 that is the panel 1, the radiation conversion layer 74, the radiation conversion layer 76, and the TFT substrate 72 that is the panel 2 are sequentially stacked along the incident direction of the radiation X. The radiation conversion layer 74 is a direct conversion type radiation conversion layer of an ISS (Irradiation Side Sampling) method as a surface reading method. On the other hand, the radiation conversion layer 76 is a PSS (Penetration Side Sampling) type indirect conversion type radiation conversion layer as a back side reading method.

The TFT substrate 70 has a function of collecting and reading (detecting) carriers (holes) that are charges generated in the radiation conversion layer 74. The TFT substrate 70 includes an insulating substrate 80 and a signal output unit 85. In this embodiment, the TFT substrate 70 also reads out the electric charge obtained by converting the fluorescence generated in the radiation conversion layer 76 by the radiation conversion layer 74. When the radiation detector 26 is an electronic reading sensor, the TFT substrate 70 has a function of collecting and reading out electrons.

Since the insulating substrate 80 absorbs the radiation X in the radiation converting layer 74 and the radiation converting layer 76, the insulating substrate 80 has a low radiation X absorbability and is a flexible electrically insulating thin substrate (about several tens of μm). The substrate having a thickness of 1 is preferable. Specifically, it is preferably a synthetic resin, aramid, bionanofiber, or film glass (ultra-thin glass) that can be wound into a roll.

The signal output unit 85 includes a capacitor 92 that is a charge storage capacitor, a field effect thin film transistor (hereinafter simply referred to as TFT) 94, and a charge collection electrode 88. The TFT 94 is a switching element that converts the electric charge accumulated in the capacitor 92 into an electric signal and outputs the electric signal.

A plurality of charge collection electrodes 88 are formed in a lattice shape (matrix shape) at intervals, and one charge collection electrode 88 corresponds to one pixel. Each charge collection electrode 88 is connected to a TFT 94 and a capacitor 92.

The capacitor 92 has a function of accumulating charges (holes) collected by the charge collection electrodes 88. The charge accumulated in each capacitor 92 is read out by the TFT 94. Thereby, the radiographic image is taken by the TFT substrate 70.

The undercoat layer 82 is formed between the radiation conversion layer 74 and the TFT substrate 70. The undercoat layer 82 preferably has rectification characteristics from the viewpoint of reducing dark current and leakage current. Therefore, the resistivity of the undercoat layer 82 is preferably 10 ⁸ Ωcm or more, and the film thickness is preferably 0.01 μm to 10 μm.

The radiation that has passed through the TFT substrate 70 passes through the undercoat layer 82 and is applied to the radiation conversion layer 74.

The radiation conversion layer 74 is a photoelectric conversion layer that is a photoconductive material that absorbs irradiated radiation and generates positive and negative charges (electron-hole carrier pairs) according to the radiation. The radiation conversion layer 74 is preferably mainly composed of amorphous Se (a-Se). The radiation conversion layer 74 includes Bi ₂ MO ₂₀ (M: Ti, Si, Ge), Bi ₄ M ₃ O ₁₂ (M: Ti, Si, Ge), Bi ₂ O ₃ , BiMO ₄ (M: Nb). , Ta, V), Bi ₂ WO ₆ , Bi ₂₄ B ₂ O ₃₉ , ZnO, ZnS, ZnSe, ZnTe, MNbO ₃ (M: Li, Na, K), PbO, HgI ₂ , PbI ₂ , CdS, CdSe, A compound containing at least one of CdTe, BiI ₃ , GaAs, and the like as a main component may be used. The radiation conversion layer 74 is preferably an amorphous material having a high dark resistance, good photoconductivity against radiation irradiation, and capable of forming a large area film at a low temperature by a vacuum deposition method.

The thickness of the radiation conversion layer 74 is preferably in the range of 100 μm or more and 2000 μm or less in the case of a photoconductive material mainly composed of a-Se as in the present embodiment, for example. In particular, for mammography applications, the range is preferably 100 μm or more and 250 μm or less. In general photographing applications, it is preferably in the range of 500 μm or more and 1200 μm or less. *

The electrode interface layer 83 has a function of blocking hole injection and a function of preventing crystallization. The electrode interface layer 83 is formed between the radiation conversion layer 74 and the overcoat layer 84.

The electrode interface layer _{_{83, CdS, CeO 2, Ta}} 2 O 5, and inorganic materials such as SiO or an organic polymer, is preferred. The layer made of an inorganic material is preferably used by adjusting the carrier selectivity by changing the composition from the stoichiometric composition or by using a multi-component composition with two or more kinds of homologous elements. As the layer made of an organic polymer, an insulating polymer such as polycarbonate, polystyrene, polyimide, and polycycloolefin can be mixed with a low molecular weight electron transport material at a weight ratio of 5% to 80%. . As such electron transporting materials, trinitrofluorene and derivatives thereof, diphenoquinone derivatives, bisnaphthyl quinone derivatives, oxazole derivatives, triazole derivatives, C _{60 (fullerene),} and those that have been mixed with carbon clusters C ₇₀ etc. are preferred. Specifically, TNF, DMDB, PBD, and TAZ are mentioned.

On the other hand, a thin insulating polymer layer can also be preferably used. For example, parylene, polycarbonate, PVA, PVP, PVB, polyester resin, and acrylic resin such as polymethyl methacrylate are preferable. In this case, the film thickness is preferably 2 μm or less, and more preferably 0.5 μm or less.

The overcoat layer 84 is formed between the electrode interface layer 83 and the bias electrode 90. The overcoat layer 84 preferably has rectification characteristics from the viewpoint of reducing dark current and leakage current. Therefore, the resistivity of the overcoat layer 84 is preferably 10 ⁸ Ωcm or more, and the film thickness is preferably 0.01 μm to 10 μm.

The bias electrode 90 has a function of applying a bias voltage to the radiation conversion layer 74, and is formed so that radiation carrying image information can pass therethrough. In the present embodiment, since the radiation detector 26 is a hole reading sensor, a positive bias voltage is supplied to the bias electrode 90 from a high voltage power supply (not shown). When the radiation detector 26 is an electronic reading sensor that reads electrons generated according to the irradiated radiation, a negative bias voltage is supplied to the bias electrode 90.

While the bias electrode 90 and the charge collection electrode 88 detect the high energy component of the radiation X in the TFT substrate 70, as described later, at least of the light (fluorescence) converted from the radiation X by the radiation conversion layer 76. Light in the sensitivity wavelength region of a-Se (for example, light in the blue wavelength region) is transmitted. For this reason, the bias electrode 90 and the charge collection electrode 88 have low X-ray absorptivity, do not cause electromigration with a-Se, and are conductive materials capable of transmitting light in the sensitivity wavelength region, for example, The transparent conductive oxide (TCO) is preferably made of a transparent conductive oxide having a high transmittance for visible light and a small resistance value. The TCO, ITO, IZO, AZO, FTO, are preferably used SnO _2, TiO 2, and ZnO ₂ and the like can. From the viewpoint of process simplicity, low resistance, and transparency, ITO (Indium Tin Oxide) is preferable. Other materials for the bias electrode 90 include Au, Ni, Cr, Pt, Ti, Al, Cu, Pd, Ag, Mg, MgAg 3% to 20% alloy, Mg-Ag intermetallic compound, MgCu 3% to 20% alloy. , And metals such as Mg—Cu intermetallic compounds can be used. In particular, Au, Pt, and Mg—Ag intermetallic compounds are preferably used. For example, when Au is used, the thickness is preferably in the range of 15 nm to 200 nm, more preferably in the range of 30 nm to 100 nm. For example, when an MgAs 3% to 20% alloy is used, the thickness is preferably in the range of 100 nm to 400 nm. In addition, since it is easy to increase resistance value when it is going to obtain the transmittance | permeability 90% or more, TCO is more preferable.

The formation method is arbitrary, but depending on the formation temperature, the a-Se of the radiation conversion layer 74 may be crystallized, so the bias electrode 90 is formed at the lowest possible temperature in order to suppress the crystallization of a-Se. It is preferable to do. For example, the bias electrode 90 is preferably formed as an organic film or organic conductor containing a metal filler by coating, roll-to-roll, ink jet, or the like. Moreover, as another method, it is preferable to form by vapor deposition by a resistance heating system. For example, the shutter is opened after the metal lump is melted in the boat by the resistance heating method, vapor deposition is performed for 15 seconds, and the cooling is once performed. This operation may be repeated a plurality of times until the resistance value of the metal thin film becomes sufficiently low.

Reading of charges (positive charge / negative charge) changed from radiation by the radiation conversion layer 74 may be performed as follows. A voltage supply unit (not shown) is connected to each charge collection electrode 88 and bias electrode 90. The voltage supply unit includes a DC power supply and a switch. The DC power supply and the switch are electrically connected to the charge collection electrodes 88 and the bias electrode 90. Here, when a switch is turned on and a DC voltage is applied from a DC power source so that each charge collecting electrode 88 is positive and the bias electrode 90 is negative, a DC electric field is generated in the radiation conversion layer 74 which is a semiconductor layer. To do. According to this DC electric field, the positive charge moves to the negative bias electrode 90 side, and the negative charge moves to the positive charge collecting electrode 88 side. As a result, the TFT substrate 70 can read the negative charges through the charge collection electrodes 88. When the TFT 94 is turned on by the gate signal from the gate line driver 132, the TFT substrate 70 responds to the negative charges through the signal line 144A. An electric signal can be output to the signal processing unit 134.

Further, when a DC voltage that causes an avalanche effect in the radiation conversion layer 74 is applied between each charge collection electrode 88 and the bias electrode 90, positive charges in the radiation conversion layer 74 and Negative charge is amplified. As a result, the number of charges read by the TFT substrate 70 (TFT 94) via each charge collecting electrode 88 can be increased.

Although the case where a DC voltage is applied so that each charge collecting electrode 88 is positive and the bias electrode 90 is negative has been described, the negative polarity is applied to each charge collecting electrode 88 and the positive DC is applied to the bias electrode 90. It goes without saying that the same effect as described above can be obtained even when a voltage is applied.

The radiation conversion layer 76 is a scintillator, and is formed so as to be laminated between the bias electrode 90 and the upper electrode 110 via the transparent insulating film 108 in the radiation detector 26 of the present embodiment. The radiation conversion layer 76 is formed by forming a phosphor that converts the radiation X incident from above or below into light and emits light. Providing such a radiation conversion layer 76 absorbs the radiation X and emits light.

The wavelength range of light emitted from the radiation conversion layer 76 is preferably a visible light range (wavelength 360 nm to 830 nm). In order to enable monochrome imaging by the radiation detector 26, it is more preferable to include a green wavelength region.

As a scintillator used for the radiation conversion layer 76, light in the a-Se sensitivity wavelength region or light in a wavelength region that can be absorbed by the TFT substrate 72 (light having a longer wavelength than light in the a-Se sensitivity wavelength region) is used. A scintillator that generates fluorescence having a relatively broad wavelength range that can be generated is desirable. Examples of such a scintillator include CsI: Na, CaWO ₄ , YTaO ₄ : Nb, BaFX: Eu (X is Br or Cl), LaOBr: Tm, and GOS. Specifically, when imaging using X-rays as radiation, those containing cesium iodide (CsI) are preferable. In particular, it is preferable to use CsI: Tl (cesium iodide to which thallium is added) or CsI: Na having an emission spectrum of 400 nm to 700 nm at the time of X-ray irradiation. Note that the emission peak wavelength in the visible light region of CsI: Tl is 565 nm.

In addition, when using the scintillator containing CsI as the radiation conversion layer 76, it is preferable to use what was formed as a strip-shaped columnar crystal structure (refer FIG. 3) by the vacuum evaporation method. The base end portion of the radiation conversion layer 76 on the TFT substrate 72 side is a non-columnar crystal portion 76 </ b> C and is in close contact with the TFT substrate 72. By providing the non-columnar crystal portion 76C, the adhesion between the radiation conversion layer 76 and the TFT substrate 72 can be improved. Further, the reflection of fluorescence can be suppressed by making the porosity of the non-columnar crystal portion 76C close to 0% or reducing the thickness thereof (for example, up to about 10 μm).

Each column constituting the columnar crystal structure 76D is formed along the incident direction of the radiation X, and a certain amount of gap is secured between adjacent columns. In addition, the CsI: Na scintillator has characteristics that the columnar crystal structure 76D is weak against humidity and the non-columnar crystal portion 76C is particularly vulnerable to humidity. (Omitted).

The upper electrode 110 is preferably made of a conductive material that is transparent at least with respect to the emission wavelength of the radiation conversion layer 76 because light generated by the radiation conversion layer 76 needs to enter the photoelectric conversion film 114. Specifically, it is preferable to use a transparent conductive oxide (TCO) having a high transmittance for visible light and a small resistance value. Although a metal thin film such as Au can be used as the upper electrode 110, the resistance value tends to increase when an attempt is made to obtain a transmittance of 90% or more, so that the TCO is preferable. For example, ITO, IZO, AZO, FTO , are preferably used SnO _2, TiO 2, and ZnO ₂ and the like can. From the viewpoint of process simplicity, low resistance, and transparency, ITO is most preferable. Note that the upper electrode 110 may have a single configuration common to all pixels, or may be divided for each pixel.

The photoelectric conversion film 114 includes an organic photoelectric conversion material that generates charges by absorbing light emitted from the radiation conversion layer 76.

The photoelectric conversion film 114 includes an organic photoelectric conversion material, absorbs the light emitted from the radiation conversion layer 76, and generates a charge corresponding to the absorbed light. In this way, the photoelectric conversion film 114 containing an organic photoelectric conversion material has a sharp absorption spectrum in the visible range. Therefore, electromagnetic waves other than light emitted by the radiation conversion layer 76 are hardly absorbed by the photoelectric conversion film 114, and noise generated by the radiation X such as X-rays absorbed by the photoelectric conversion film 114 is effectively suppressed. can do.

The organic photoelectric conversion material of the photoelectric conversion film 114 is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the radiation conversion layer 76 in order to absorb light emitted from the radiation conversion layer 76 most efficiently. Ideally, the absorption peak wavelength of the organic photoelectric conversion material and the emission peak wavelength of the radiation conversion layer 76 are ideal, but if the difference between the two is small, the light emitted from the radiation conversion layer 76 is sufficiently absorbed. Is possible. Specifically, the difference between the absorption peak wavelength of the organic photoelectric conversion material and the emission peak wavelength with respect to the radiation of the radiation conversion layer 76 is preferably within 10 nm, and more preferably within 5 nm.

Examples of organic photoelectric conversion materials that can satisfy such conditions include quinacridone organic compounds and phthalocyanine organic compounds. For example, since the absorption peak wavelength of quinacridone in the visible region is 560 nm, if quinacridone is used as the organic photoelectric conversion material and CsI (Tl) is used as the material of the radiation conversion layer 76, the difference in the peak wavelength is within 5 nm. Is possible. Thereby, the amount of charge generated in the photoelectric conversion film 114 can be substantially maximized.

In order to suppress an increase in dark current, it is preferable to provide at least one of the electron blocking film 116 and the hole blocking film 118, and it is more preferable to provide both. The electron blocking film 116 can be provided between the lower electrode 112 and the photoelectric conversion film 114. The electron blocking film 116 suppresses an increase in dark current caused by injection of electrons from the lower electrode 112 to the photoelectric conversion film 114 when a bias voltage is applied between the lower electrode 112 and the upper electrode 110. it can. An electron donating organic material can be used for the electron blocking film 116. On the other hand, the hole blocking film 118 can be provided between the photoelectric conversion film 114 and the upper electrode 110. In the hole blocking film 118, when a bias voltage is applied between the lower electrode 112 and the upper electrode 110, holes are injected from the upper electrode 110 into the photoelectric conversion film 114 and dark current increases. Can be suppressed. An electron-accepting organic material can be used for the hole blocking film 118.

The lower electrode 112 is substantially the same as the charge collection electrode 88, and a plurality of lower electrodes 112 are formed in a lattice shape (matrix shape) at intervals, and one lower electrode 112 corresponds to one pixel. Each lower electrode 112 is connected to the TFT 122 and the capacitor 120 of the signal output unit 102. Note that an insulating film 103 is interposed between the signal output unit 102 and the lower electrode 112.

The signal output unit 102 corresponds to the lower electrode 112, a capacitor 120 that is a charge storage capacity for storing the charge transferred to the lower electrode 112, and switching that converts the charge stored in the capacitor 120 into an electrical signal and outputs the electric signal TFT122 which is an element is formed. The region where the capacitor 120 and the TFT 122 are formed has a portion overlapping the lower electrode 112 in plan view. In order to minimize the plane area of the radiation detector 26 (pixel), it is desirable that the region where the capacitor 120 and the TFT 122 are formed is completely covered by the lower electrode 112.

It should be noted that the signal output unit 102 with a low possibility of reaching the radiation X is replaced with the other imaging elements such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor, TFT, May be combined. Further, it may be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to the gate signal of the TFT.

A filter may be provided between the radiation conversion layer 74 (bias electrode 90) and the radiation conversion layer 76. The filter detects a high energy component of the radiation X in the radiation conversion layer 76 and transmits at least light in the sensitivity wavelength region of the radiation conversion layer (a-Se) 74 out of the fluorescence generated in the radiation conversion layer 76. . Therefore, it is preferable that the filter is made of a material that has low absorption of radiation X and can transmit the light. Further, the bias electrode 90 may have the function of the filter.

Note that the radiation detector 26 is not limited to the above-described one, and may be, for example, a flexible substrate. As the flexible substrate, it is preferable to apply a substrate using ultra-thin glass by a recently developed float method as a base material in order to improve the radiation transmittance. As for the ultra-thin glass that can be applied at this time, for example, “Asahi Glass Co., Ltd.,“ Successfully developed the world's thinnest 0.1 mm thick ultra-thin glass by the float method ”, [online], [2011 Aug. 20 search], Internet <URL: http://www.agc.com/news/2011/0516.pdf> ”.

The radiation X (radiation X transmitted through the subject 30) irradiated to the radiation detector 26 of the electronic cassette 20 from the radiation generator 12 (radiation irradiation source 22A) is a TFT substrate 70, a radiation conversion layer 74, a radiation conversion layer. 76 and the TFT substrate 72 are transmitted in this order.

At this time, the direct conversion radiation conversion layer 74 including a semiconductor layer such as a-Se can generate a high-quality radiation image as compared with the indirect conversion radiation conversion layer 76 including a scintillator. However, a semiconductor layer such as a-Se has a characteristic that it is difficult to absorb a high energy component of the radiation X as compared with a scintillator. The K edge of a-Se exists on the lower energy side than the K edge of GOS (Gd ₂ O ₂ S), CsI, or Ba (for example, BaFBr, BaFCl) used in the scintillator. Therefore, the radiation conversion layer 74 (a-Se) easily absorbs the low energy component (low pressure energy) of the radiation X, but hardly absorbs the high energy component (high pressure energy). On the other hand, the radiation conversion layer 76 (GOS, CsI, or Ba scintillator) has a characteristic that it easily absorbs the high-pressure energy of the radiation X but hardly absorbs the low-pressure energy as compared with the a-Se semiconductor layer.

In the present embodiment, the low-pressure energy (low energy component) of the radiation X is the radiation X corresponding to the low voltage when the tube voltage of the radiation irradiation source 22A of the radiation generator 12 is relatively low. The energy component of The low-pressure energy is easily absorbed by the mammo, soft tissue, tumor, or the like of the subject 30. The high-voltage energy (high energy component) of the radiation X refers to the energy component of the radiation X corresponding to the high voltage when the tube voltage of the radiation irradiation source 22A is relatively high. The high-pressure energy is easily absorbed by the bone part or the like of the subject 30.

The radiation detector 26 according to the present embodiment only needs to include two TFT substrates (panel 1 and panel 2) stacked along the irradiation direction of the radiation X, and the configuration is as described above (FIG. 2A). , See FIG. 2B). Another example of the radiation detector 26 of the present embodiment will be described.

4A to 4C show other examples when the direct conversion type radiation conversion layer 74, the panel 1, and the panel 2 are provided as in the radiation detector 26 described above (FIGS. 2A and 2B). Show. The panel 1 is a TFT substrate 70 that reads out charges from the direct conversion type radiation conversion layer 74. The panel 2 is a TFT substrate 72 that reads out charges from the indirect conversion type radiation conversion layer 76.

In FIG. 4A, a radiation conversion layer 74, a PSS TFT substrate 70 as the panel 1, an ISS TFT substrate 72 as the panel 2, and a radiation conversion layer 76 are stacked in this order from the radiation X irradiation side. The radiation detector 26 is shown. In this case, the TFT substrate 70 and the TFT substrate 72 may not be separate TFT substrates, but may be a single substrate (panel) having the functions of both the TFT substrate 70 and the TFT substrate 72.

4B shows an ISS TFT substrate 70 as a panel 1, a radiation conversion layer 74, an ISS TFT substrate 72 as a panel 2, and a radiation conversion layer 76 in order from the side irradiated with the radiation X. A stacked radiation detector 26 is shown. Further, FIG. 4C shows a radiation conversion layer 74, a PSS TFT substrate 70 as the panel 1, a radiation conversion layer 76 as the panel 1, and a PSS TFT substrate 72 as the panel 2. A stacked radiation detector 26 is shown.

Which radiation detector 26 is to be used may be determined according to the characteristics and specifications of the radiation image to be photographed by the electronic cassette 20. In the radiation detector 26 shown in FIGS. 2A, 2B and 4A to 4C described above, the direct conversion radiation conversion layer 74 is irradiated with the radiation X more than the indirect conversion radiation conversion layer 76. Although it arrange | positions so that it may be provided in the near (radiation irradiation source 22A), it is not restricted to this. For example, the radiation conversion layer 74 and the radiation conversion layer 76 may be disposed in reverse. Since it is preferable to provide a radiation conversion layer sensitive to low-pressure energy on the side closer to the radiation X irradiation side (radiation irradiation source 22A), the radiation shown in FIGS. 2A, 2B and 4A to 4C described above is used. It is preferable to arrange like the detector 26.

Moreover, in the radiation detector 26 of this Embodiment provided with the panel 1 and the panel 2, and two radiation conversion layers, both of the two radiation conversion layers are good also as the direct type radiation conversion layer 74, or indirectly. A radiation conversion layer 76 of a type may be used. In this case, the sensitivity of the two radiation conversion layers to the radiation X is preferably different. An example of an indirect radiation conversion layer 76 is shown in FIG. 5A.

In FIG. 5A, an ISS TFT substrate 72A, a radiation conversion layer 76A, a radiation conversion layer 76B, and a PSS TFT substrate 72B are stacked as the panel 1 in order from the side irradiated with the radiation X. The radiation detector 26 is shown. In this case, the radiation conversion layer 76A laminated closer to the radiation X irradiation side (radiation irradiation source 22A) is used as the radiation conversion layer 76 sensitive to low-pressure energy, and the radiation conversion layer 76B is radiation sensitive to high-pressure energy. The conversion layer 76 is preferable.

Further, a filter 75 such as a copper plate may be provided between the radiation conversion layer 76A and the radiation conversion layer 76B. By providing the filter 75, two images with substantially different tube voltages can be obtained by one imaging, and therefore it is preferable to provide the filter 75 when generating an energy subtraction image.
FIG. 5B shows an example in which both of the two radiation conversion layers are direct radiation conversion layers 74. In FIG. 5B, an ISS TFT substrate 70A, a radiation conversion layer 74A, a radiation conversion layer 74B, and a PSS TFT substrate 70B as the panel 2 are stacked in order from the side irradiated with the radiation X. The radiation detector 26 is shown. The radiation detector 26 shown in FIG. 5B includes a panel 1 in which a radiation conversion layer (a-Se) 74A is directly deposited on a TFT substrate 70A, and a panel in which a radiation conversion layer (a-Se) 74B is directly deposited on a TFT substrate 70B. 2 is provided. Panel 1 and panel 2 are in close contact with each other through an insulating layer 77. Panels 1 and 2 can apply a voltage to the radiation conversion layer (a-Se) 74 (74A, 74B), respectively.

Furthermore, the radiation detector 26 may be provided with one radiation conversion layer between the panel 1 and the panel 2. In this case, a direct radiation conversion layer 74 may be provided (see FIG. 6A), or an indirect radiation conversion layer 76 may be provided (see FIG. 6B).

Next, a circuit configuration of the electronic cassette 20 that is a radiographic imaging apparatus including the radiation detector 26 according to the present embodiment described above will be described. FIG. 7 shows a schematic circuit configuration diagram of an example of the electronic cassette 20. FIG. 7 shows a state in which the electronic cassette 20 is viewed in plan from the radiation X irradiation side.

The electronic cassette 20 includes a cassette control unit 130, a gate line driver 132, a signal processing unit 134, and a plurality of pixels 140 arranged in a matrix in the matrix direction. Each pixel 140 includes a TFT substrate (a part of the TFT substrate) of the panel 1 of the radiation detector 26 and a TFT substrate (a part of the TFT substrate) of the panel 2. In the case of the radiation detector 26 shown in FIG. 2A, a radiation conversion layer 74 (a part of the radiation conversion layer 74) and a radiation conversion layer 76 (a part of the radiation conversion layer 76) are further included.

The electronic cassette 20 includes a plurality of

gate lines

142A and 142B parallel to the row direction of the pixels 140 and a plurality of

signal lines

144A and 144B parallel to the column direction of the pixels 140. The gate lines 142A and 142B are connected to the gate line driver 132, and the

signal lines

144A and 144B are connected to the signal processing unit 134.

The gate line 142A and the signal line 144A are provided in the panel 1, and the gate line 142B and the signal line 144B are provided in the panel 2. That is, for each pixel 140 arranged in the row direction, one gate line 142A connected to panel 1 (for example, TFT 94 of TFT substrate 70) and panel 2 (for example, TFT 122 of TFT substrate 72) are connected. One gate line 142B to be connected and a total of two gate lines 142 are provided. Further, for each pixel 140 arranged in the column direction, one signal line 144A connected to the panel 1 (for example, the TFT 94 of the TFT substrate 70) and the panel 2 (for example, the TFT 122 of the TFT substrate 72) are connected. One signal line 144B to be connected and two signal lines 144 in total are provided.

The TFTs of the panel 1 and the TFT of the panel 2 are sequentially turned on for each row, and the charges converted and accumulated from the radiation in the radiation conversion layer 74, and the radiation conversion layer 76 is converted from radiation to fluorescence, and the photoelectric conversion film In 114, the electric charge converted and accumulated from the fluorescence can be read out as an electric signal. Specifically, by sequentially outputting an ON signal to the gate line 142A and the gate line 142B according to a predetermined frame rate from the gate line driver 132 (such as a frame rate instructed from the console 16), each panel is output. The TFT is turned on. When the TFT of each panel is turned on, an electric signal corresponding to the electric charge accumulated in the signal line 144A and the signal line 144B flows.

The charge (electrical signal) that has flowed through the signal line 144A and the signal line 144B flows out to the signal processing unit 134. The signal processing unit 134 amplifies the flowed-in charge (analog electrical signal) by an amplifier circuit (not shown), and then performs A / D conversion by an A / D (analog / digital) conversion circuit (not shown). The signal processing unit 134 outputs the radiation image (first image and second image, details will be described later) converted into a digital signal to the cassette control unit 130.

Further, the function of the electronic cassette 20 provided with the radiation detector 26 of the present embodiment will be described. The electronic cassette 20 of the present embodiment includes a first image (first image information) generated based on the charges read by the panel 1 and a first image generated based on the charges read by the panel 2. It has a function of combining two images (second image information) and transmitting the combined image (combined image information) to the radiation image processing device 14. In FIG. 8, the functional block diagram corresponding to the said function of an example of the electronic cassette 20 is shown.

The electronic cassette 20 of the present embodiment includes a cassette control unit 130, a first image information generation unit 150, a second image information generation unit 152, a composite image information generation unit 154, an interpolation image generation unit 156, a transmission unit 157, and a reception unit. 158 and a storage unit 159. The first image information generation unit 150 generates a first image (first image information) based on the electric charges read by the panel 1. The second image information generation unit 152 generates a second image (second image information) based on the charges read by the panel 2. The composite image information generation unit 154 generates the composite image information by combining the first image information and the second image information.

The cassette control unit 130 has a function of controlling the operation of the entire electronic cassette 20, and includes a CPU, a ROM, a RAM, and an HDD, like the console 16 of the radiographic imaging system 10 described above. The CPU has a function of controlling the operation of the entire electronic cassette 20. Various programs including a control program used by the CPU are stored in advance in the ROM. The RAM has a function of temporarily storing various data. An HDD (Hard Disk Drive) has a function of storing and holding various data.

The transmission unit 157 and the reception unit 158 have a function of transmitting and receiving various types of information including radiographic image information and a composition ratio to and from the radiographic image processing apparatus 14 and the console 16 by wireless communication or wired communication. ing.

The cassette control unit 130 is configured to take a radiographic image based on an imaging menu including imaging conditions and the like received by the receiving unit 158 via the console 16 or the radiographic image processing device 14. 1 and panel 2 are controlled. Specifically, the panel 1 (for example, the TFT 94 of the TFT substrate 70) is driven to capture the first image, and the read charge is output. Further, the panel 2 (for example, the TFT 122 of the TFT substrate 72) is driven so as to capture the second image, and the read charge is output. In capturing a moving image, electric charges are read from each of the panel 1 and the panel 2 at a frame rate determined in advance according to a shooting menu or the like. Note that the frame rate at which the panel 1 reads the charges (captures the first image) and the frame rate at which the panel 2 reads the charges (captures the first image) may be the same or different. Also good. The frame rate may be determined according to shooting conditions and the characteristics of the panel 1 and the panel 2.

1st image information generation part 150 generates the 1st image information which shows the 1st image which is a radiographic image based on the electric charge read by panel 1. As shown in FIG. Further, the second image information generation unit 152 generates second image information indicating a second image that is a radiation image based on the electric charges read by the panel 2. When capturing a moving image, a plurality of first images (first image information) and second images (second image information) corresponding to the frame rate are generated as described above.

The composite image information generation unit 154 combines the first image information generated by the first image information generation unit 150 and the second image information generated by the second image information generation unit 152 from the cassette control unit 130. A composite image (composite image information) is generated by combining at a ratio. At this time, the synthesized image information generation unit 154 synthesizes the first image information and the second image information that have been accumulated or electrified at the same timing. Note that the charge accumulation timing and the accumulation period are not limited to the same, but the charge accumulation timing and the accumulation end timing are determined in advance from one accumulation timing (accumulation start timing and accumulation end timing) even when the accumulation periods overlap or do not overlap. It may be considered that the timing is the same, for example, when charge accumulation is performed within a predetermined period (period within the allowable range). It may be determined depending on the image quality desired by the radiogram interpreter. Note that a method for generating a composite image is not particularly limited. For example, the composite image may be synthesized by adding or dividing the charge amount (electric signal corresponding to the charge amount) for each pixel.

When synthesizing the first image information obtained by the panel 1 and the second image information obtained by the panel 2, it is simply synthesized according to the characteristics of the panels 1 and 2, the characteristics of the radiation conversion layer, the imaging conditions, and the like. If (addition of image information) is performed, a radiographic image having an image quality desired by the image interpreter may not be obtained, or the image quality may deteriorate. In particular, when capturing a moving image, generally, the dose per shot (one frame: one frame) is reduced in order to avoid an increase in the exposure dose of the subject 30. Therefore, the charge accumulation time per shot is shorter than when a still image is taken. On the other hand, in the electronic cassette 20 of the present embodiment, image information (first image information and second image information) obtained from each of the panel 1 and the panel 2 is synthesized to create a moving image as a synthesized image. As a result, the image quality of the moving image can be improved. However, the image quality and the like of the first image and the second image are easily affected by the characteristics of the panels 1 and 2, the characteristics of the radiation conversion layer, the imaging conditions, and the like. In some cases, the radiographic image having the desired image quality cannot be obtained or the image quality is deteriorated.

When the radiation detector 26 shown in FIG. 4A is used, a radiation image (first image) obtained by a TFT substrate 70 (TFT substrate corresponding to a PSS radiation conversion layer), which is a panel 1 having high sensitivity, is normally used. Diagnosis (interpretation) is performed using one image Further, when improving the accuracy of diagnosis or when it is difficult to see the object of interest (tumor, tumor, etc.) to be observed only with the first image, it corresponds to the TFT substrate 72 (panel of ISS type radiation conversion layer). It is preferable to add (synthesize) the radiation image (second image) obtained by the TFT substrate). Therefore, in the case where such a radiation detector 26 is used, in the present embodiment, for example, imaging conditions such as during normal imaging, whether to improve diagnosis accuracy, or whether there is a user preference setting, and The first image information and the second image information are synthesized at a synthesis ratio according to the conditions specified by the user.

Also, the image quality of the radiographic image obtained may vary depending on the dose and energy of the radiation X irradiated to the electronic cassette 20 (radiation detector 26). For this reason, in the present embodiment, the composition ratio is determined in advance for the photographing conditions (mainly tube voltage), the radiographer's desire, and the like. FIG. 9A schematically shows a case where the irradiated radiation X has low energy. In this case, the amount of light emitted on the incident side in the radiation conversion layer is relatively larger than the amount of light emitted on the non-incident side. Since the propagation distance is long in the panel 2 on the non-incident side, the image may be blurred in the second image obtained by the panel 2 on the non-incident side. Therefore, in such a case, it is preferable to display the first image obtained from the first image information as a moving image without adding the second image information. In addition, when displaying the radiographic image (first image or second image) obtained by one of the panel 1 and the panel 2 in this way, the image information of the radiographic image (here, the second image) that is not added is displayed. The composition ratio may be set to “0”.

On the other hand, FIG. 9B schematically shows a case where the irradiated radiation X has high energy. In this case, the radiation conversion layer has a sufficient amount of light emission even on the non-incident side, and the second image obtained by the panel 2 on the non-incident side without much difference between the light emission amount on the incident side and the light emission amount on the non-incident side. The image blur is reduced. Accordingly, in such a case, the first image information and the second image information may be added (for example, added at an equivalent combining ratio), or the panel 2 on the anti-incident side may be emphasized (compositing on the anti-incident side). The ratio may be increased).

FIG. 10 shows the relationship between the distance from the radiation X irradiation side (the thickness of the radiation conversion layer between the panel 1 and the panel 2) and the absorption rate of the radiation X. The absorption rate of the radiation X varies depending on the energy of the irradiated radiation X. Therefore, in the present embodiment, when such a radiation detector 26 is used, the first image information and the second image information are combined at a combination ratio corresponding to the energy of the radiation X.

In the case of the radiation detector 26 (electronic cassette 20) shown in FIGS. 2A and 2B, the first image information is mainly a TFT substrate that reads out charges converted from radiation by the direct conversion type radiation conversion layer 74. 70 is obtained as panel 1. The second image information is obtained by using the TFT substrate 72 that reads out the charges converted from the radiation mainly by the indirect conversion type radiation conversion layer 76 as the panel 2. In such a case, when the first image information and the second image information are combined, the radiation conversion layer 74 and the radiation conversion layer 76 have different characteristics as described above. Therefore, a high-quality moving image can be obtained by combining with weighting (composition ratio) according to characteristics. For example, the radiation conversion layer 74 is excellent in the absorption of low-pressure energy of the radiation X, and is preferably used for photographing a soft tissue or a tumor of the subject 30. On the other hand, the radiation conversion layer 76 is excellent in the absorption of the high-pressure energy of the radiation X, and is preferably used for photographing the bone part of the subject 30. In such a case, it is possible to obtain a radiographic image (referred to as an energy subtraction image) in which one image of a soft tissue or a tumor or the like and a bone portion that is a hard tissue is emphasized and the other image is removed. For this reason, in the present embodiment, a composition ratio set in accordance with what the radiographer wants to observe (what to emphasize) is used. The energy subtraction image is not limited to the case where the radiation detector 26 shown in FIGS. 2A and 2B is used, and can be obtained using the radiation detector 26 shown in FIG. 5 as described above. Therefore, in the present embodiment, when such a radiation detector 26 is used, the first image information is obtained by a composite ratio according to whether an energy subtraction image is displayed or soft tissue or hard tissue is emphasized. And the second image information are combined.

Further, the characteristics of the panel 1 and the panel 2 are different, for example, when the panel 1 corresponds to the direct conversion type radiation conversion layer 74 and the panel 2 corresponds to the indirect conversion type radiation conversion layer 76. If so, the relationship between the irradiated radiation X and the resolution of the captured radiographic image may be different. Therefore, in the present embodiment, when such a radiation detector 26 is used, the first image information and the second image information are synthesized at a synthesis ratio corresponding to a desired resolution, energy of the radiation X, and the like.

As described above, the first configuration corresponding to the configuration of the radiation detector 26 (characteristics of the panels 1 and 2), the tube voltage of the radiation source 22A, the imaging conditions such as the imaging region and procedure, the preference of the interpreter, and the like. A composition ratio between the image information and the second image information is determined. In the present embodiment, the correspondence between the imaging conditions, the radiogram interpreter (for example, ID for identifying the radiogram interpreter), and the composition ratio is stored in the storage unit 159. The cassette control unit 130 reads out the composition ratio corresponding to the imaging condition or the like instructed from the console 16 from the storage unit 159 and instructs the composite image information generation unit 154.

The interpolation image generation unit 156, when there is no image information (second image information or first image information) to be combined with the first image information or the second image information read by the combined image information generation unit 154, the interpolation image Is generated. In this case, the composite image information generation unit 154 generates composite image information by combining the first image information or the second image information and the generated interpolation image.

The composite image (composite image information) may be transmitted (transferred) by either wireless communication or wired communication, but the two systems are made independent using a plurality of routes (

communication routes

157A, 157B). Transfer is also preferable from the viewpoint of speeding up. Further, for example, whether to perform wireless communication or wired communication may be determined according to the information amount (transfer amount) and transfer speed of the image.

Next, the radiation image processing function in the radiation image capturing system 10 (radiation image processing apparatus 14) of the present embodiment will be described. In the present embodiment, display of a composite image received from the electronic cassette 20 is controlled as radiation image processing. FIG. 11 is a functional block diagram for explaining an example of the radiation image processing function. The block diagram categorizes the radiographic image processing functions by function and does not limit the hardware configuration.

As shown in FIG. 11, the radiographic image capturing system 10 (radiological image processing apparatus 14) of the present embodiment includes a display control unit 160, a reception unit 166, a composite chart generation unit 168, a storage unit 169, a reception unit 68A, and A transmission unit 68B is provided. In FIG. 11, the display 23 (operation panel 24) and the display 50 (operation panel 54) are shown in common.

In the radiographic imaging system 10 (radiation image processing apparatus 14) of the present embodiment, the composite image information and the composite ratio received from the electronic cassette 20 by the reception unit 68A are stored in the storage unit 169. In addition, the radiation image processing apparatus 14 displays the composite image read from the storage unit 169 and generates a composite chart indicating a composite ratio corresponding to the composite ratio read from the storage unit 169 with the composite chart generation unit 168. In the present embodiment, the configuration corresponding to the reception function in the I / F unit 68 is referred to as a reception unit 68A.

The display control unit 160 has a function of controlling the display of radiation images and the like on the display 23 and the display 50. In the present embodiment, the composite image 184 stored in the storage unit 17 and the composite chart 186 generated by the composite chart generation unit 168 are displayed in the display areas of the display 23 and the display 50. A specific example of the display state of the display 23 and the display 50 is shown in FIG.

The composite chart 186 shows a composite ratio between the first image information and the second image information. In the present embodiment, the radiogram interpreter can set the composition ratio by viewing the composite image 184 displayed on the display 23 or the display 50 and inputting an instruction to the composite chart 186. The accepting unit 166 has a function of accepting the composition ratio input by the radiogram interpreter using the composition chart 186. The composition ratio received by the reception unit 166 is output to the electronic cassette 20 by the transmission unit 68B. The electronic cassette 20 synthesizes the first image information and the second image information based on the received composition ratio. As a result, at the time of interpretation of the composite image, the interpreter can instruct the composition ratio based on the displayed composite image, so that the composite image of the image quality desired by the interpreter can be displayed. When the composition ratio is received by the reception unit 166, a composition chart is generated by the composition chart generation unit 168 so as to indicate the received composition ratio, and is displayed on the display (23, 50) under the control of the display control unit 160. .

Next, the radiographic imaging process in the radiographic imaging system 10 (electronic cassette 20) of this embodiment will be described in detail. A flowchart of an example of the radiographic image capturing process of the present embodiment is shown in FIG. The radiographic image capturing process is performed by executing a radiographic image capturing process program by the CPU of the cassette control unit 130. In the present embodiment, the program is stored in advance in a storage unit (not shown) in the cassette control unit 130, a ROM, or the like, but may be downloaded from an external stem (RIS), a CD-ROM, a USB, or the like. It may be. The radiographic image capturing process shown in FIG. 13 is executed when a radiographic image is captured.

In step S100, it is determined whether shooting is moving image shooting or still image shooting. Note that pre-photographing such as positioning during video shooting is regarded as still image shooting. In the case of still image shooting, the determination is negative and the process proceeds to step S102.

In the next step S102, the first image information generation unit 150 generates first image information. In the next step S104, the second image information generating unit 152 generates second image information.

In the next step S106, a composition ratio is acquired in accordance with the above-described shooting conditions and conditions (hereinafter simply referred to as conditions) preferred by the interpreter. In the present embodiment, since the correspondence between the condition and the composition ratio is stored in the storage unit 159, the composition ratio corresponding to the condition is acquired from the storage unit 159. In the next step S108, the composite image information generation unit 154 combines the first image information and the second image information with the acquired composition ratio to generate composite image information, and then the process proceeds to step S118.

On the other hand, in the case of moving image shooting, the determination is affirmed and the process proceeds to step S110. In step S110, the first image information generation unit 150 generates first image information. In the next step S112, the second image information generation unit 152 generates second image information. Further, in the next step S114, a combination ratio corresponding to the condition is acquired in the same manner as in step S106 described above.

In the next step S116, the first image information and the second image information are synthesized with the synthesis ratio acquired by the synthesized image information generation unit 154 to generate synthesized image information (details will be described later).

In the next step S118, the composite image information generated by the composite image information generation unit 154 is output to the radiation image processing apparatus 14. In the next step S120, it is determined whether or not to end this process. If there is still a radiographic image to be captured (for example, during the capturing of a moving image), the determination is negative, the process returns to step S110, and this process is repeated. On the other hand, if the process is to be ended, the determination is affirmed and this process is ended.

Next, the composite image information generation process in step S116 described above will be described in detail. FIG. 14 shows a flowchart of an example of the composite image information generation process of the present embodiment.

In step S200, whether the frame rate of the first image information and the frame rate of the second image information are the same is determined based on the shooting conditions and the like. The frame rate of the first image information is a frame rate when the first image information is captured by the panel 1. The frame rate of the second image information is a frame rate when the second image information is captured by the panel 2. A specific example of the frame rate of the electronic cassette 20 including the radiation detector 26 shown in FIGS. 2A and 2B is shown in FIG. FIG. 15 shows a case where the number of frames of panel 1 and panel 2 is 6 (corresponding to 6 frames, corresponding to F11 to F16 and F21 to F26), assuming that the number of frames is the same. Further, as a case where the number of frames is not the same, a case where the number of frames of the panel 2 is 3 (three, corresponding to F2'1 to F2'3) is shown. For example, when the panel 2 is set as a panel (TFT substrate) mainly used for taking a still image and the charge accumulation time is long, the number of frames may be different in this way. In addition, for example, the direct conversion type radiation conversion layer 74 and the indirect conversion type radiation conversion layer 76 have different charge amounts according to the radiation X, so that it is necessary to make the charge accumulation times different. May be the same.

In the present embodiment, as shown in FIG. 15, during moving image shooting, radiation is continuously emitted from the radiation irradiation source 22A until shooting of all shots (frames) (charge accumulation) is completed. Continuous irradiation for irradiating the cassette 20 is performed.

If the frame rates are the same, the determination is affirmed and the process proceeds to step S202. In step S202, the composite image information is generated by combining the first image information and the second image information of the same frame by the composite image information generation unit 154, and then the present process ends.

On the other hand, if the frame rates are not the same, the result is negative and the process proceeds to step S204. In step S204, it is determined whether to generate a composite image. In the case of shooting with different frame rates, for example, the frame F2′1 of the panel 2 corresponding to the frame F12 of the panel 1 has accumulated charges at the same timing, or cannot be regarded as accumulated. One image and the second image are not combined. On the other hand, even if the frame rates are different, for example, the frame F2'1 of the panel 2 corresponding to the frame F11 of the panel 1 stores charges at the same timing. As described above, in the present embodiment, the first image information and the second image information that are considered to have accumulated charges or accumulated at the same timing are synthesized.

In the case of generating a composite image, the determination is affirmed and the process proceeds to step S206, where the composite image information generation unit 154 combines the first image information and the second image information that are considered to have accumulated charges or accumulated at the same timing. Then, after generating the composite image information, the present process is terminated.

On the other hand, if a composite image is not generated, the determination is negative and the process proceeds to step S208. In step S208, interpolation image information is generated. For example, as the interpolated image information for the frame F12 of the panel 1, the interpolated image information is generated using the second image information corresponding to the frame F2′1 of the panel 2 and the second image information corresponding to the frame F2′2. . Note that the method of generating the interpolated image information is not particularly limited, and for example, an intermediate value of two pieces of second image information (an intermediate value of pixel values of each pixel) may be used.

In the next step S210, the first image information or the second image information and the generated interpolated image information are combined to generate combined image information, and then the present process ends. In the example described above, the composite image information is generated by combining the first image information corresponding to the frame F12 and the interpolated image information.

Next, radiographic image processing in the radiographic image processing apparatus 14 of the radiographic image capturing system 10 of the present exemplary embodiment will be described in detail. A flowchart of an example of the radiographic image processing of the present embodiment is shown in FIG. This process is performed by executing a radiographic image processing program by the CPU of the system control unit 60. In the present embodiment, the program is stored in advance in a storage unit (not shown) in the system control unit 60, a ROM, or the like, but may be downloaded from an external stem (RIS), a CD-ROM, a USB, or the like. It may be.

In step S300, it is determined whether or not the composite image information is received from the electronic cassette 20. If it has not been received, it is denied and enters a standby state. On the other hand, if it is received, the determination is affirmative and the process proceeds to step S302. In step S302, a composite image corresponding to the received composite image information is displayed on the display (23, 50). In the next step S304, a composite chart indicating a composite ratio is generated by the composite chart generation unit 168, and a composite chart 186 is displayed.

In the next step S306, it is determined whether a composition ratio has been accepted. If the reception unit 166 has not received a composite ratio instruction input, the determination is negative and the process proceeds to step S310. On the other hand, when an instruction input for a composition ratio is received, the determination is affirmed and the process proceeds to step S308. After the composition ratio received by the reception unit 166 is transmitted to the electronic cassette 20, the process proceeds to step S310. The electronic cassette 20 receives the composition ratio transmitted in step S308 (step S400), and sets the received composition ratio (instructs the composite image information generation unit 154) (step S402).

In step S310, it is determined whether or not to end this process. If not, the determination is negative and the process returns to step S300 to repeat this process. On the other hand, if the process is to be ended, the determination is affirmed and this process is ended.

As described above, in the electronic cassette 20 provided in the radiographic imaging system 10 of the present embodiment, the radiation detector 26 includes two panels (the panel 1 arranged on the radiation X irradiation side and the non-radiation X non-radioscope). A panel 2) arranged on the irradiation side is provided. The radiation detector 26 generates first image information corresponding to the charges read by the panel 1 and second image information corresponding to the charges read by the panel 2. In addition, the radiation detector 26 combines the first image information and the second image information that can be regarded as charges accumulated or accumulated at the same timing according to conditions such as imaging conditions or conditions preferred by the reader. Composite image information synthesized by the ratio is generated and transmitted to the radiation image processing apparatus 14. The radiographic image processing device 14 performs control so that a composite image corresponding to the received composite image information is displayed on the display 23 or the display 50.

As described above, in the present embodiment, the radiation detector 26 includes the panel 1 and the panel 2, and the first image information and the second image information obtained by the radiation detector 26 are combined at a combination ratio corresponding to the conditions. As a result, the image quality of the radiation image can be improved. In order to synthesize at a synthesis ratio according to conditions, for example, the image quality of the radiation image is improved as compared with the case where the first image information captured by the panel 1 is simply interpolated by the second image information captured by the panel 2. be able to.

In the present embodiment, a case has been described in which continuous irradiation is continuously performed by irradiating the electronic cassette 20 (radiation detector 26) with the radiation X from the radiation irradiation source 22A during moving image shooting (see FIG. 15). Not limited to. For example, you may make it perform what is called pulse irradiation (refer FIG. 17) which irradiates the radiation X intermittently according to the accumulation | storage period of an electric charge. When the frame rate corresponding to the first image information is different from the frame rate corresponding to the second image information, if the radiation X is irradiated during the transfer of the charge with the slower frame rate, the appropriate radiation image information (First image information or second image information) may not be obtained. Therefore, when the frame rates are different as described above, it is preferable to perform continuous irradiation as in the present embodiment. When the radiographic image capturing system 10 (the radiographic image processing apparatus 14) determines that the frame rates are different based on the imaging conditions and the like, it is preferable to control the radiation generating apparatus 12 so that continuous irradiation is performed.

When pulse irradiation of radiation X is performed when the frame rates are different, radiation X is irradiated during the charge accumulation period, and outside the accumulation period, it is opened and closed according to each charge accumulation period so that radiation X is irradiated. It is preferable to provide a shutter or the like.

In addition, the configuration of the radiographic image capturing system 10, the radiographic image processing device 14, the electronic cassette 20, the radiation detector 26, and the like described in the present embodiment are examples. Needless to say, these can be changed according to the situation within the scope of the present invention.

Further, the radiation described in the present embodiment is not particularly limited, and X-rays, γ-rays, and the like can be applied.

The entire disclosure of Japanese application 2011-239680 is incorporated herein by reference.

All documents, patent applications, and technical standards mentioned in this specification are to the same extent as if each individual document, patent application, and technical standard were specifically and individually stated to be incorporated by reference, Incorporated herein by reference.

DESCRIPTION OF SYMBOLS 10 Radiographic imaging system 14 Radiation image processing apparatus 16 Console 70 TFT substrate (TFT substrate substrate according to direct conversion type)
72 TFT substrate (TFT substrate substrate corresponding to indirect conversion type)
74 Radiation conversion layer (direct conversion type)
76 Radiation conversion layer (indirect conversion type)
20 Electronic cassette 26 Radiation detector 68 I / F unit, 68A Reception unit 130 Cassette control unit 150 First image information generation unit 152 Second image information generation unit 154 Composite image information generation unit 156 Interpolation image generation unit 157 Transmission unit 160 Display Control unit 168 Composite chart generation unit

Claims

A radiation conversion unit that converts radiation into at least one of charge and fluorescence in accordance with the irradiated radiation, and a first charge detection unit connected to the radiation conversion unit that detects the charge converted and accumulated by the radiation conversion unit Alternatively, the first substrate including any one of the second charge detection units connected to the radiation conversion unit for detecting the accumulated charges by converting the fluorescence converted by the radiation conversion unit, the first charge detection unit Or a radiation detector including a second substrate including any one of the second charge detection units;
Generating means for generating first image information based on the charge detected by the first substrate, and generating second image information based on the charge detected by the second substrate;
One of the first image information and the second image information generated by the generating unit is regarded as the same timing as the charge accumulation timing when the one image information is generated by the generating unit. Combining means for generating combined image information obtained by combining the other image information generated based on the charge accumulated at a predetermined timing;
Transmitting means for transmitting the synthesized image information synthesized by the synthesizing means to the outside;
A radiographic imaging apparatus comprising:
The radiographic imaging apparatus according to claim 1, wherein the synthesizing unit synthesizes at a synthesis ratio corresponding to at least one of imaging conditions registered in advance and conditions predetermined by a user.
The said production | generation means produces | generates the said 1st image information and the said 2nd image information at the frame rate predetermined according to the said video recording, when video recording is performed. Radiographic imaging device.
When the predetermined frame rates of the first image information and the second image information are different from each other, an interpolation unit that generates interpolation image information so as to match any one of the predetermined frame rates is provided, The radiographic image capturing apparatus according to claim 3, wherein the synthesizing unit generates synthesized image information using the interpolated image information.
The radiographic imaging apparatus according to any one of claims 1 to 4, wherein the transmission unit transmits a composite ratio when the composite image information is combined together with the composite image information.
The radiographic imaging apparatus according to any one of claims 1 to 5, wherein the transmission unit transmits the first image information and the second image information through different paths.
The radiation conversion unit includes: a first radiation conversion layer laminated on the first substrate; and a second radiation conversion layer having sensitivity to radiation laminated on the second substrate different from that of the first radiation conversion layer. Furthermore, the radiographic imaging device of any one of Claims 1-6.
The radiographic imaging apparatus according to claim 7, wherein the first radiation conversion layer is a direct conversion type that converts radiation into electric charge, and is provided on the radiation irradiation side with respect to the second radiation conversion layer.
The first radiation conversion layer is more sensitive to low energy components of radiation than the second radiation conversion layer, and is provided on the radiation irradiation side of the second radiation conversion layer. Or the radiographic imaging apparatus of Claim 8.
The predetermined timing includes the timing at which at least a part of the charge accumulation period overlaps the charge accumulation period when the one image information is generated by the generation unit, and the one of the generation unit by the generation unit. The radiographic imaging device according to any one of claims 1 to 9, wherein the radiographic imaging device is at least one of timings within a predetermined range from a charge accumulation timing when image information is generated.
Receiving means for receiving composite image information transmitted from the radiographic image capturing apparatus according to any one of claims 1 to 10;
Control means for controlling the display means to display a composite image corresponding to the composite image information received by the receiving means;
A radiographic image processing apparatus comprising:
12. The radiographic image processing apparatus according to claim 11, wherein the control means controls the display means to display a composite ratio image indicating a composite ratio of the composite image.
Accepting means for accepting setting of a composition ratio of the composite image;
A composition ratio transmitting means for transmitting the composition ratio accepted by the accepting means to the radiographic imaging device;
The radiographic image processing apparatus of Claim 11 or Claim 12 provided with these.
The radiographic imaging device according to any one of claims 1 to 10, and
The radiographic image processing apparatus according to any one of claims 11 to 13, which receives composite image information from the radiographic image capturing apparatus.
Radiographic imaging system equipped with.
A radiation irradiation device;
When the predetermined frame rates of the first image information and the second image information generated by the generation unit of the radiographic image capturing apparatus are different from each other, the radioactivity detector is continuously connected to the radiation detector during a period during which the moving image is captured. Radiation irradiation control means for controlling the radiation irradiation apparatus so that radiation is irradiated;
The radiographic imaging system according to claim 14, comprising:
A radiation conversion unit that converts radiation into at least one of charge and fluorescence in accordance with the irradiated radiation, and a first charge detection unit connected to the radiation conversion unit that detects the charge converted and accumulated by the radiation conversion unit Alternatively, the first substrate including any one of the second charge detection units connected to the radiation conversion unit for detecting the accumulated charges by converting the fluorescence converted by the radiation conversion unit, the first charge detection unit Alternatively, the first image information is generated based on the charge detected by the first substrate using a radiation detector including a second substrate including any one of the second charge detection units, and the second A generating step of generating second image information based on the charge detected by the substrate;
One image information of the first image information and the second image information generated by the generation step is regarded as the same timing as the charge accumulation timing when the one image information is generated by the generation step. A combining step for generating combined image information obtained by combining the other image information generated based on the charge accumulated at a predetermined timing;
A transmission step of transmitting the composite image information synthesized by the synthesis step to the outside;
A radiographic imaging method comprising:
A radiation conversion unit that converts radiation into at least one of charge and fluorescence in accordance with the irradiated radiation, and a first charge detection unit connected to the radiation conversion unit that detects the charge converted and accumulated by the radiation conversion unit Alternatively, the first substrate including any one of the second charge detection units connected to the radiation conversion unit for detecting the accumulated charges by converting the fluorescence converted by the radiation conversion unit, the first charge detection unit Alternatively, the radiation detector includes a second substrate including any one of the second charge detection units, and generates first image information based on the charges detected by the first substrate. Generation means for generating second image information based on the detected charge, image information of one of the first image information and the second image information generated by the generation means, and the generation Combined image information obtained by combining the other image information generated based on the charge accumulated at a predetermined timing that is regarded as the same timing as the charge accumulation timing when the one image information is generated in the stage. A radiographic imaging apparatus comprising: a synthesizing unit that generates; and a transmission unit that transmits the synthesized image information synthesized by the synthesizing unit to the outside, for causing the computer to function as the generating unit and the synthesizing unit. Radiation imaging program.