JP2012048169A - Radiation image photographing device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiation image photographing device capable of preventing charging due to vibration at the time of transportation of a radiation detector.SOLUTION: Conductive rubber 46 is attached to a surface opposite to a surface of a radiation detector 20 where the radiation detector 20 is attached to a top plate 41B of a housing 41 of an electronic cassette 40, and is supported by a surface opposite to the top plate 41B of the housing 41. Detecting a resistance value of the conductive rubber 46 obtains a strain amount of the radiation detector, whereby a degradation state of the radiation detector can be also obtained.

Description

  The present invention relates to a radiographic image capturing apparatus, and more particularly to a radiographic image capturing apparatus that captures a radiographic image indicated by radiation that has passed through an imaging target.

  In recent years, radiation detectors such as flat panel detectors (FPDs) that can arrange radiation sensitive layers on TFT (Thin Film Transistor) active matrix substrates and convert radiation directly into digital data have been put into practical use. A portable radiographic image capturing apparatus (hereinafter also referred to as “electronic cassette”) that captures a radiographic image represented by irradiated radiation has been put into practical use. The radiation detectors used in the above-mentioned electronic cassettes include, as a method for converting radiation, an indirect conversion method in which radiation is converted into light by a scintillator and then converted into electric charges in a semiconductor layer such as a photodiode, or radiation is converted into amorphous selenium. There are direct conversion systems that convert charges into semiconductor layers, etc., and there are various materials that can be used for the semiconductor layer in each system.

  As a technique related to this type of radiographic imaging apparatus, Patent Document 1 discloses a radiation detection apparatus including a flexible radiation detector that detects radiation transmitted through a subject and converts it into radiographic image information. The radiation detector is irradiated with the radiation that has passed through the subject, the scintillator that converts the radiation incident through the irradiation surface into visible light, and the visible light as the electrical signal. A solid-state detection element that converts the light into a radiation detector, covering at least the radiation detector, and shielding light incident on the radiation detector, wherein the light shielding means includes the radiation. While the detector has a distortion amount measurement sensor in a portion facing the imaging region on the irradiation surface, the sensitivity and the sensitivity at the radiation detector are based on the detection value from the distortion amount measurement sensor. Radiation detecting apparatus is disclosed, characterized in that it comprises a correcting means for correcting at least one of the dark current.

  Patent Document 2 discloses a detection surface, a radiation detection unit that obtains a radiation image based on the radiation that has reached the detection surface, a load detection unit that detects a load applied on the detection surface, and the load detection unit. And a warning means for issuing a warning in accordance with the load amount detected by the radiographic apparatus.

JP 2010-85121 A JP 2002-357664 A

  By the way, in the conventional electronic cassette, there is a technique for directly attaching a radiation detector to the top plate of the apparatus housing for the purpose of thinning the apparatus in order to improve its portability. Since the vibration when carrying the cassette is transmitted to the radiation detector, there is a problem that the radiation detector is easily charged with static electricity.

  On the other hand, the techniques disclosed in Patent Document 1 and Patent Document 2 can improve the quality of the radiation image and prevent the destruction of the apparatus, but with regard to charging due to the vibration of the radiation detector. Since no consideration is given to this problem, it is powerless.

  The present invention has been made to solve the above problems, and an object of the present invention is to provide a radiographic imaging apparatus capable of preventing the radiation detector from being charged.

  In order to achieve the above object, a radiographic imaging device according to claim 1 is provided with a housing having a top plate irradiated with radiation emitted from a radiation source and transmitted through a subject, and attached to the top plate. A flat radiation detector that is provided inside the housing in a state of being taken and takes a radiographic image indicated by radiation transmitted through the top plate, and is attached to the top plate of the radiation detector A conductive rubber attached to a surface opposite to the surface; and a support member for supporting the conductive rubber on a surface opposite to the top plate of the housing.

  According to the radiographic imaging device of claim 1, the top plate is attached to the top plate of the housing having the top plate that is irradiated with the radiation emitted from the radiation source and transmitted through the subject. A flat radiation detector that captures a radiographic image indicated by the radiation that has passed through is provided inside the housing.

  Here, in the present invention, conductive rubber is attached to a surface opposite to the surface attached to the top plate of the radiation detector, while the conductive rubber is supported by the support member on the top of the casing. It is supported on the surface opposite to the plate.

  Thus, according to the radiographic imaging device of claim 1, the top plate of the housing is placed on the surface of the radiation detector attached to the top plate opposite to the surface attached to the top plate. Since the conductive rubber supported on the opposite surface is attached, the vibration of the radiation detector that occurs when carrying the radiographic imaging device can be suppressed. As a result, the radiation detector caused by the vibration Can be prevented.

  In the present invention, as in the invention described in claim 2, the conductive rubber may be grounded. Thereby, the static electricity which arises in a radiation detector can be discharged effectively.

  Further, according to the present invention, as in the invention according to claim 3, the conductive rubber is attached to a central portion of the surface opposite to the surface attached to the top plate of the radiation detector. May be. Thereby, static electricity generated in the radiation detector can be discharged more effectively.

  Moreover, as for this invention, the said conductive rubber may have foamability like invention of Claim 4. Thereby, the anti-vibration property with respect to a radiation detector can be improved more.

  Further, according to the present invention, as in the invention described in claim 5, the radiation detector generates a light when irradiated with radiation, and a charge is received by receiving the light generated by the scintillator. You may have a sensor part comprised including the organic photoelectric conversion material to generate | occur | produce. Thereby, the impact resistance of a radiographic imaging apparatus can be improved.

  In the present invention, as in the invention described in claim 6, the radiation detector may be detachably attached to the top plate. Thereby, a housing | casing can be exchanged efficiently.

  Further, according to the present invention, as in the invention described in claim 7, the radiation detector is bonded to the top plate so that an internal space is formed between the radiation detector and the top plate. The adhesive member may be further provided with a ventilation unit that communicates the internal space and the outside and prevents foreign matter from entering the internal space from the outside.

  According to the present invention, since the radiation detector is bonded to the top plate so that an internal space is formed between the radiation detector and the top plate using the adhesive member, the contact of the adhesive member to the radiation detector and the top plate is achieved. Even if air remains on the surface, the remaining air can be released to the internal space. Further, since the internal space communicates with the outside through the ventilation means, the pressure in the internal space and the external atmospheric pressure can be kept constant even when the atmospheric pressure changes. Therefore, it can prevent that the adhesiveness of the radiation detector with respect to a top plate falls by atmospheric pressure change.

  Further, since the ventilation means prevents foreign matters from entering the internal space from the outside, it is possible to eliminate the concern that foreign matters such as metal pieces that absorb radiation enter the internal space and are displayed in the radiation image. . Accordingly, it is possible to suppress the contamination of foreign matters that leads to the deterioration of the quality of the radiation image.

  In particular, the invention according to claim 7 may be a communication path in which the ventilation means is formed in the adhesive member and communicates in a state where the internal space and the outside are bent.

  According to the present invention, since the communication path is bent, it is possible to prevent the foreign matter from entering the internal space even when foreign matter flows into the communication path from the outside together with air. This is because the mass of the foreign matter is larger than the mass of air, so that the foreign matter cannot follow the flow of air flowing through the bent portion of the communication path. Further, since the communication path is formed in the adhesive member, the foreign matter is likely to adhere to the wall surface of the communication path. Accordingly, the foreign matter that can no longer follow the air flow at the bent portion of the communication passage is reliably captured by the wall surface of the communication passage having adhesiveness. As a result, it is possible to more reliably prevent foreign matter from entering the internal space.

  Moreover, as for this invention, the said top plate may be comprised with the material containing a reinforced fiber resin like invention of Claim 8. Thereby, compared with the case where a top plate is comprised with a carbon single-piece | unit etc., the intensity | strength of a top plate can be made high.

  In particular, in the invention described in claim 8, as in the invention described in claim 9, the reinforcing fiber resin may be a carbon fiber reinforced plastic. As a result, it is possible to increase the thermal conductivity of the top plate as compared with the case where the top plate is made of carbon alone, and as a result, image unevenness due to temperature unevenness of the radiation image obtained by the radiation detector is reduced. Can be suppressed.

  By the way, in the radiographic imaging device in which the radiation detector is attached to the top plate of the casing, since the imaging is usually performed with the imaging part pressed against the top plate, the radiation detector also responds to the press. Distortion may occur. On the other hand, it is known that a radiation detector deteriorates when distortion occurs, and when the distortion occurs continuously or intermittently, the degree of deterioration gradually increases. Thus, when the deterioration of the radiation detector progresses, the deterioration of the image quality of the radiographic image obtained by photographing also progresses.

  Accordingly, the present invention provides a detection means for detecting a resistance value of the conductive rubber and an amount of distortion of the radiation detector based on the resistance value detected by the detection means, as in the invention described in claim 10. And derivation means for deriving. Thereby, it is possible to grasp the state of deterioration of the radiation detector using the distortion amount derived by the deriving means, and it is possible to take measures according to the state of deterioration.

  According to the radiographic imaging device of the present invention, the radiation detector attached to the top plate is disposed on the surface opposite to the surface attached to the top plate, and on the surface opposite to the top plate of the housing. Since the supported conductive rubber is attached, it is possible to suppress the vibration of the radiation detector that occurs when carrying the radiographic imaging device, and as a result, the radiation detector can be prevented from being charged due to the vibration. The effect of being able to be obtained is obtained.

It is a block diagram which shows the structure of the radiation information system which concerns on embodiment. It is a side view which shows an example of the arrangement | positioning state of each apparatus in the radiography room of the radiographic imaging system which concerns on embodiment. It is a cross-sectional schematic diagram which shows schematic structure of the 3 pixel part of the radiation detector which concerns on embodiment. It is the cross-sectional side view which showed schematically the structure of the signal output part of 1 pixel part of the radiation detector which concerns on embodiment. It is a schematic plan view which shows the structure of the radiation detector which concerns on embodiment. It is a perspective view which shows the structure of the electronic cassette concerning embodiment. It is a schematic plan view which shows the structure of the scintillator which concerns on embodiment. It is a section side view showing the composition of the electronic cassette concerning an embodiment. It is a cross-sectional bottom view which shows the internal structure of the housing | casing of the electronic cassette concerning embodiment. It is a partially expanded sectional bottom view which shows the internal structure of the housing | casing of the electronic cassette concerning embodiment. It is explanatory drawing which shows the state which peels a radiation detector from a top plate in the electronic cassette which concerns on embodiment. It is a block diagram which shows the principal part structure of the electrical system of the radiographic imaging system which concerns on embodiment. It is a schematic diagram which shows the structure of the distortion degradation coefficient information which concerns on embodiment, time degradation coefficient information, and temperature degradation coefficient information. It is a flowchart which shows the flow of a process of the radiographic imaging processing program which concerns on embodiment. It is the schematic which shows an example of the initial stage information input screen which concerns on embodiment. It is a flowchart which shows the flow of a process of the degradation degree derivation | leading-out process program which concerns on embodiment. It is a cross-sectional side view for demonstrating the surface reading system and back surface reading system of the radiation to a radiation detector. It is a partially expanded sectional bottom view which shows the modification of the internal structure of the housing | casing of the electronic cassette concerning embodiment. It is a schematic plan view which shows the modification of the structure of the scintillator which concerns on embodiment.

  DESCRIPTION OF EMBODIMENTS Hereinafter, embodiments for carrying out the present invention will be described in detail with reference to the drawings. Here, a description will be given of an example in which the present invention is applied to a radiation information system that is a system for comprehensively managing information handled in a radiology department in a hospital.

  First, the configuration of a radiation information system (hereinafter referred to as “RIS” (Radiology Information System)) 100 according to the present embodiment will be described with reference to FIG.

  The RIS 100 is a system for performing information management such as medical appointment reservation and diagnosis record in the radiology department, and constitutes a part of a hospital information system (hereinafter referred to as “HIS” (Hospital Information System)). .

  The RIS 100 includes a plurality of radiography requesting terminal devices (hereinafter referred to as “terminal devices”) 140, a RIS server 150, and a radiographic imaging system (or an operating room) installed in a radiographic room (or operating room) in a hospital. (Hereinafter referred to as “imaging system”) 104, which are connected to an in-hospital network 102 composed of a wired or wireless LAN (Local Area Network). The RIS 100 constitutes a part of the HIS provided in the same hospital, and an HIS server (not shown) for managing the entire HIS is also connected to the in-hospital network 102.

  The terminal device 140 is used by doctors and radiographers to input and browse diagnostic information and facility reservations, and radiographic image capturing requests and imaging reservations are also performed via the terminal device 140. Each terminal device 140 includes a personal computer having a display device, and can communicate with the RIS server 150 via the hospital network 102.

  On the other hand, the RIS server 150 receives an imaging request from each terminal device 140 and manages a radiographic imaging schedule in the imaging system 104, and includes a database 150A.

  Database 150A includes patient (subject) attribute information (name, sex, date of birth, age, blood type, weight, patient ID (Identification), etc.), medical history, medical history, radiation images taken in the past, etc. Information related to the patient, identification number (ID information) of the electronic cassette 40 (to be described later) used in the imaging system 104, model, size, sensitivity, usable imaging part (content of imaging request that can be supported), date of start of use , Information about the electronic cassette 40 such as the number of times of use, and environment information indicating an environment in which a radiographic image is taken using the electronic cassette 40, that is, an environment in which the electronic cassette 40 is used (for example, a radiographic room or an operating room) It is comprised including.

  The imaging system 104 captures a radiographic image by an operation of a doctor or a radiographer according to an instruction from the RIS server 150. The imaging system 104 includes a radiation generator 120 that irradiates a subject with radiation X (see also FIG. 6) that has been dosed according to the exposure conditions from a radiation source 121 (see also FIG. 2), and a subject. Electrons that incorporate a radiation detector 20 (see also FIG. 6) that absorbs radiation X that has passed through a region to be imaged by the person and generates charges, and generates image information indicating a radiation image based on the amount of charges generated. A cassette 40, a cradle 130 for charging a battery built in the electronic cassette 40, and a console 110 for controlling the electronic cassette 40 and the radiation generator 120 are provided.

  The console 110 acquires various types of information included in the database 150A from the RIS server 150, stores them in the HDD 116 (see FIG. 12) described later, and uses the information as necessary to use the electronic cassette 40 and the radiation generator 120. Control.

  FIG. 2 shows an example of the arrangement state of each device in the radiation imaging room 180 of the imaging system 104 according to the present embodiment.

  As shown in the figure, the radiation imaging room 180 has a standing table 160 used when performing radiography in a standing position and a prone table 164 used when performing radiography in a lying position. The space in front of the standing stand 160 is set as a photographing position 170 of the subject when performing radiography in the standing position, and the space above the supine stand 164 is when performing radiography in the prone position. The imaging position 172 of the subject.

  The standing stand 160 is provided with a holding unit 162 that holds the electronic cassette 40, and the electronic cassette 40 is held by the holding unit 162 when a radiographic image is taken in the standing position. Similarly, the holding table 164 is provided with a holding unit 166 that holds the electronic cassette 40, and the electronic cassette 40 is held by the holding unit 166 when a radiographic image is taken in the lying position.

  Further, in the radiation imaging room 180, the radiation source 121 is placed around a horizontal axis (see FIG. 5) in order to enable radiation imaging in a standing position and radiation imaging in a lying position by radiation from a single radiation source 121. 2 is provided, and a support moving mechanism 124 is provided which can be rotated in the vertical direction (arrow b direction in FIG. 2) and can be moved in the horizontal direction (arrow c direction in FIG. 2). It has been. Here, the support moving mechanism 124 includes a drive source that rotates the radiation source 121 around a horizontal axis, a drive source that moves the radiation source 121 in the vertical direction, and a drive source that moves the radiation source 121 in the horizontal direction. Each is provided (not shown).

  On the other hand, the cradle 130 is formed with an accommodating portion 130 </ b> A capable of accommodating the electronic cassette 40.

  When the electronic cassette 40 is not in use, the built-in battery is charged in a state of being housed in the housing portion 130A of the cradle 130. When a radiographic image is taken, the electronic cassette 40 is taken out from the cradle 130 by a radiographer or the like, so If it is in the upright position, it is held in the holding part 162 of the standing table 160, and if it is in the lying position, it is held in the holding part 166 of the standing table 164.

  Here, in the imaging system 104 according to the present embodiment, various types of information are transmitted and received between the radiation generation apparatus 120 and the console 110 and between the electronic cassette 40 and the console 110 by wireless communication.

  The electronic cassette 40 is not used only in a state where it is held by the holding part 162 of the standing base 160 or the holding part 166 of the prone base 164. When photographing, it can be used in a state where it is not held by the holding unit.

  Next, the configuration of the radiation detector 20 according to the present embodiment will be described. FIG. 3 is a schematic cross-sectional view schematically showing the configuration of the three pixel portions of the radiation detector 20 according to the present exemplary embodiment.

  As shown in the figure, in the radiation detector 20 according to the present embodiment, a signal output unit 14, a sensor unit 13, and a scintillator 8 are sequentially stacked on an insulating substrate 1. The pixel unit is configured by the sensor unit 13. A plurality of pixel units are arranged on the substrate 1, and the signal output unit 14 and the sensor unit 13 in each pixel unit are configured to overlap each other.

  The scintillator 8 is formed on the sensor unit 13 via the transparent insulating film 7, and forms a phosphor that emits light by converting radiation incident from above (opposite side of the substrate 1) or from below into light. It is a thing. Providing such a scintillator 8 absorbs the radiation transmitted through the subject and emits light.

  The wavelength range of light emitted by the scintillator 8 is preferably a visible light range (wavelength 360 nm to 830 nm), and in order to enable monochrome imaging by the radiation detector 20, the wavelength range of green is included. Is more preferable.

  Specifically, the phosphor used in the scintillator 8 preferably contains cesium iodide (CsI) when imaging using X-rays as radiation, and has an emission spectrum of 420 nm to 600 nm during X-ray irradiation. It is particularly preferable to use CsI (Ti) (cesium iodide added with titanium). Note that the emission peak wavelength of CsI (Ti) in the visible light region is 565 nm.

  The sensor unit 13 includes an upper electrode 6, a lower electrode 2, and a photoelectric conversion film 4 disposed between the upper and lower electrodes. The photoelectric conversion film 4 absorbs light emitted from the scintillator 8 and generates charges. It is composed of an organic photoelectric conversion material.

Since it is necessary for the upper electrode 6 to cause the light generated by the scintillator 8 to be incident on the photoelectric conversion film 4, it is preferable that the upper electrode 6 be made of a conductive material that is transparent at least with respect to the emission wavelength of the scintillator 8. 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 6, TCO is preferable because it tends to increase the resistance value when it is desired to obtain a transmittance of 90% or more. For example, ITO, IZO, AZO, FTO, SnO ₂ , TiO ₂ , ZnO _{2 and the} like can be preferably used, and ITO is most preferable from the viewpoint of process simplicity, low resistance, and transparency. Note that the upper electrode 6 may have a single configuration common to all the pixel portions, or may be divided for each pixel portion.

  The photoelectric conversion film 4 absorbs light emitted from the scintillator 8 and generates electric charges according to the absorbed light. The photoelectric conversion film 4 may be formed of a material that generates charges when irradiated with light. For example, the photoelectric conversion film 4 can be formed of amorphous silicon, an organic photoelectric conversion material, or the like. The photoelectric conversion film 4 containing amorphous silicon has a wide absorption spectrum and can absorb light emitted by the scintillator 8. If the photoelectric conversion film 4 includes an organic photoelectric conversion material, it has a sharp absorption spectrum in the visible range, and electromagnetic waves other than light emitted by the scintillator 8 are hardly absorbed by the photoelectric conversion film 4, and radiation such as X-rays. Can be effectively suppressed noise generated by the absorption by the photoelectric conversion film 4. In the present embodiment, the photoelectric conversion film 4 includes an organic photoelectric conversion material.

  The organic photoelectric conversion material constituting the photoelectric conversion film 4 is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the scintillator 8 in order to absorb light emitted by the scintillator 8 most efficiently. Ideally, the absorption peak wavelength of the organic photoelectric conversion material matches the emission peak wavelength of the scintillator 8, but if the difference between the two is small, the light emitted from the scintillator 8 can be sufficiently absorbed. . 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 scintillator 8 is preferably within 10 nm, and more preferably within 5 nm.

  Examples of the organic photoelectric conversion material that can satisfy such conditions include quinacridone-based organic compounds and phthalocyanine-based organic compounds. For example, since the absorption peak wavelength in the visible region of quinacridone is 560 nm, if quinacridone is used as the organic photoelectric conversion material and CsI (Ti) is used as the material of the scintillator 8, the difference in peak wavelength can be made within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 4 can be substantially maximized.

  Next, the photoelectric conversion film 4 applicable to the radiation detector 20 according to the present embodiment will be specifically described.

  The electromagnetic wave absorption / photoelectric conversion site in the radiation detector 20 according to the present embodiment is configured by an organic layer including a pair of electrodes 2 and 6 and an organic photoelectric conversion film 4 sandwiched between the electrodes 2 and 6. be able to. More specifically, this organic layer is a part that absorbs electromagnetic waves, a photoelectric conversion part, an electron transport part, a hole transport part, an electron blocking part, a hole blocking part, a crystallization preventing part, an electrode, and an interlayer contact improvement. It can be formed by stacking or mixing parts.

  The organic layer preferably contains an organic p-type compound or an organic n-type compound.

  The organic p-type semiconductor (compound) is a donor organic semiconductor (compound) mainly represented by a hole-transporting organic compound and refers to an organic compound having a property of easily donating electrons. More specifically, an organic compound having a smaller ionization potential when two organic materials are used in contact with each other. Accordingly, any organic compound can be used as the donor organic compound as long as it is an electron-donating organic compound.

  An organic n-type semiconductor (compound) is an acceptor organic semiconductor (compound) mainly represented by an electron-transporting organic compound and refers to an organic compound having a property of easily accepting electrons. More specifically, the organic compound having the higher electron affinity when two organic compounds are used in contact with each other. Accordingly, as the acceptor organic compound, any organic compound can be used as long as it is an electron-accepting organic compound.

  The materials applicable as the organic p-type semiconductor and organic n-type semiconductor and the configuration of the photoelectric conversion film 4 are described in detail in Japanese Patent Application Laid-Open No. 2009-32854, and thus the description thereof is omitted.

  The thickness of the photoelectric conversion film 4 is preferably as large as possible in terms of absorbing light from the scintillator 8. However, when the thickness is more than a certain level, the photoelectric conversion film 4 is generated in the photoelectric conversion film 4 by a bias voltage applied from both ends of the photoelectric conversion film 4. Since electric field strength is reduced and charges cannot be collected, the thickness is preferably 30 nm to 300 nm, more preferably 50 nm to 250 nm, and particularly preferably 80 nm to 200 nm.

  In the radiation detector 20 shown in FIG. 3, the photoelectric conversion film 4 has a single-sheet configuration common to all pixel units, but may be divided for each pixel unit.

  The lower electrode 2 is a thin film divided for each pixel portion. The lower electrode 2 can be made of a transparent or opaque conductive material, and aluminum, silver, or the like can be suitably used.

  The thickness of the lower electrode 2 can be, for example, 30 nm or more and 300 nm or less.

  In the sensor unit 13, by applying a predetermined bias voltage between the upper electrode 6 and the lower electrode 2, one of electric charges (holes, electrons) generated in the photoelectric conversion film 4 is moved to the upper electrode 6. The other can be moved to the lower electrode 2. In the radiation detector 20 of the present embodiment, a wiring is connected to the upper electrode 6, and a bias voltage is applied to the upper electrode 6 through this wiring. In addition, the polarity of the bias voltage is determined so that electrons generated in the photoelectric conversion film 4 move to the upper electrode 6 and holes move to the lower electrode 2, but this polarity is reversed. May be.

  The sensor unit 13 constituting each pixel unit only needs to include at least the lower electrode 2, the photoelectric conversion film 4, and the upper electrode 6. In order to suppress an increase in dark current, the electron blocking film 3 and hole blocking are performed. It is preferable to provide at least one of the films 5, and it is more preferable to provide both.

  The electron blocking film 3 can be provided between the lower electrode 2 and the photoelectric conversion film 4. When a bias voltage is applied between the lower electrode 2 and the upper electrode 6, electrons are transferred from the lower electrode 2 to the photoelectric conversion film 4. It is possible to suppress the dark current from increasing due to the injection of.

  An electron donating organic material can be used for the electron blocking film 3.

  The material actually used for the electron blocking film 3 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 4 and the like, and 1.3 eV or more from the work function (Wf) of the material of the adjacent electrode. Those having a large electron affinity (Ea) and an Ip equivalent to or smaller than the ionization potential (Ip) of the material of the adjacent photoelectric conversion film 4 are preferable. The material applicable as the electron donating organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, and thus the description thereof is omitted.

  The thickness of the electron blocking film 3 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to surely exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 13. It is 50 nm or more and 100 nm or less.

  The hole blocking film 5 can be provided between the photoelectric conversion film 4 and the upper electrode 6. When a bias voltage is applied between the lower electrode 2 and the upper electrode 6, the hole blocking film 5 is transferred from the upper electrode 6 to the photoelectric conversion film 4. It is possible to suppress the increase in dark current due to the injection of holes.

  An electron-accepting organic material can be used for the hole blocking film 5.

  The thickness of the hole blocking film 5 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to surely exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 13. Is from 50 nm to 100 nm.

  The material actually used for the hole blocking film 5 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 4 and the like, and 1.3 eV from the work function (Wf) of the material of the adjacent electrode. As described above, it is preferable that the ionization potential (Ip) is large and that the Ea is equal to or larger than the electron affinity (Ea) of the material of the adjacent photoelectric conversion film 4. Since the material applicable as the electron-accepting organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.

  In addition, when a bias voltage is set so that holes move to the upper electrode 6 and electrons move to the lower electrode 2 among the charges generated in the photoelectric conversion film 4, the electron blocking film 3 and the hole blocking are set. The position of the film 5 may be reversed. Moreover, it is not necessary to provide both the electron blocking film 3 and the hole blocking film 5. If either one is provided, a certain degree of dark current suppressing effect can be obtained.

  A signal output unit 14 is formed on the surface of the substrate 1 below the lower electrode 2 of each pixel unit. FIG. 4 schematically shows the configuration of the signal output unit 14.

  As shown in the figure, the signal output unit 14 according to the present embodiment corresponds to the lower electrode 2, and a capacitor 9 that accumulates the charges transferred to the lower electrode 2, and the electric charges accumulated in the capacitor 9 are electrically A field effect thin film transistor (Thin Film Transistor, hereinafter simply referred to as a thin film transistor) 10 that converts the signal into a signal and outputs the signal is formed. The region in which the capacitor 9 and the thin film transistor 10 are formed has a portion that overlaps the lower electrode 2 in a plan view. With such a configuration, the signal output unit 14 and the sensor unit 13 in each pixel unit are connected to each other. There will be overlap in the thickness direction. In order to minimize the plane area of the radiation detector 20 (pixel portion), it is desirable that the region where the capacitor 9 and the thin film transistor 10 are formed is completely covered by the lower electrode 2.

  The capacitor 9 is electrically connected to the corresponding lower electrode 2 through a wiring made of a conductive material penetrating an insulating film 11 provided between the substrate 1 and the lower electrode 2. Thereby, the electric charge collected by the lower electrode 2 can be moved to the capacitor 9.

In the thin film transistor 10, a gate electrode 15, a gate insulating film 16, and an active layer (channel layer) 17 are stacked, and a source electrode 18 and a drain electrode 19 are formed on the active layer 17 at a predetermined interval. . In the radiation detector 20, the active layer 17 is formed of an amorphous oxide. The amorphous oxide constituting the active layer 17 is preferably an oxide containing at least one of In, Ga, and Zn (for example, In—O-based), and at least two of In, Ga, and Zn. An oxide containing In (eg, In—Zn—O, In—Ga, or Ga—Zn—O) is more preferable, and an oxide containing In, Ga, and Zn is particularly preferable. As the In—Ga—Zn—O-based amorphous oxide, an amorphous oxide whose composition in a crystalline state is represented by InGaO ₃ (ZnO) _m (m is a natural number less than 6) is preferable, and InGaZnO is particularly preferable. ₄ is more preferable.

  If the active layer 17 of the thin film transistor 10 is formed of an amorphous oxide, it will not absorb radiation such as X-rays, or even if it is absorbed, it will remain extremely small, so that noise is generated in the signal output unit 14. It can be effectively suppressed.

  Here, both the amorphous oxide constituting the active layer 17 of the thin film transistor 10 and the organic photoelectric conversion material constituting the photoelectric conversion film 4 can be formed at a low temperature. Therefore, the substrate 1 is not limited to a substrate having high heat resistance such as a semiconductor substrate, a quartz substrate, and a glass substrate, and a flexible substrate such as plastic, aramid, or bionanofiber can also be used. Specifically, flexible materials such as polyesters such as polyethylene terephthalate, polybutylene phthalate, polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, poly (chlorotrifluoroethylene), etc. A conductive substrate can be used. If such a plastic flexible substrate is used, it is possible to reduce the weight, which is advantageous for carrying around, for example.

  In addition, the substrate 1 is provided with an insulating layer for ensuring insulation, a gas barrier layer for preventing permeation of moisture and oxygen, an undercoat layer for improving flatness or adhesion to electrodes, and the like. May be.

  On the other hand, since aramid can be applied at a high temperature process of 200 ° C. or more, the transparent electrode material can be cured at a high temperature to reduce its resistance, and it can also be used for automatic mounting of a driver IC including a solder reflow process. Moreover, since aramid has a thermal expansion coefficient close to that of ITO (Indium Tin Oxide) or a glass substrate, there is little warping after manufacturing and it is difficult to crack. In addition, aramid can form a substrate thinner than a glass substrate or the like. The substrate may be formed by laminating an ultrathin glass substrate and aramid.

  The bionanofiber is a composite of a cellulose microfibril bundle (bacterial cellulose) produced by bacteria (Acetobacter Xylinum) and a transparent resin. The cellulose microfibril bundle has a width of 50 nm and a size of 1/10 of the visible light wavelength, and has high strength, high elasticity, and low thermal expansion. By impregnating and curing a transparent resin such as an acrylic resin or an epoxy resin in bacterial cellulose, a bio-nanofiber having a light transmittance of about 90% at a wavelength of 500 nm can be obtained while containing 60 to 70% of the fiber. Bionanofiber has a low coefficient of thermal expansion (3-7ppm) comparable to silicon crystals, and is as strong as steel (460MPa), highly elastic (30GPa), and flexible, compared to glass substrates, etc. The substrate 1 can be formed thinly.

  In the present embodiment, the TFT substrate 30 is formed on the substrate 1 by sequentially forming the signal output unit 14, the sensor unit 13, and the transparent insulating film 7, and the light-absorbing adhesive resin is formed on the TFT substrate 30. The radiation detector 20 is formed by pasting the scintillator 8 using, for example.

  As shown in FIG. 5, the TFT substrate 30 includes a pixel unit 32 including the sensor unit 13, the capacitor 9, and the thin film transistor 10 described above in a certain direction (the row direction in FIG. 5) and the certain direction. A plurality of two-dimensional shapes are provided in the intersecting direction (column direction in FIG. 5).

  Further, the radiation detector 20 extends in the predetermined direction (row direction), and extends in the intersecting direction (column direction) with a plurality of gate wirings 34 for turning on and off each thin film transistor 10. A plurality of data wirings 36 for reading out charges through the thin film transistor 10 in the on state are provided.

  The radiation detector 20 has a flat plate shape and a quadrilateral shape having four sides on the outer edge in a plan view, more specifically, a rectangular shape.

  Next, the configuration of the electronic cassette 40 according to the present embodiment will be described. FIG. 6 is a perspective view showing the configuration of the electronic cassette 40 according to the present exemplary embodiment.

  As shown in the figure, an electronic cassette 40 according to the present embodiment includes a flat casing 41 made of a material that transmits radiation, and has a waterproof and airtight structure. A space (external space) A for accommodating various components is formed inside the housing 41, and the subject is transmitted through the space from the irradiation surface side of the housing 41 irradiated with the radiation X. The radiation detector 20 for detecting the radiation X and the lead plate 43 for absorbing the back scattered radiation of the radiation X are arranged in this order.

  Here, in the electronic cassette 40 according to the present exemplary embodiment, the area corresponding to the arrangement position of the radiation detector 20 on one flat surface of the housing 41 is a quadrilateral imaging area 41A capable of detecting radiation. Has been. The surface having the imaging region 41A of the housing 41 is a top plate 41B in the electronic cassette 40. In the electronic cassette 40 according to the present embodiment, as shown in FIG. 8, the radiation detector 20 includes a TFT substrate. 30 is disposed on the top plate 41B side, and is attached to the inner surface of the casing 41 of the top plate 41B (the surface opposite to the surface on which radiation of the top plate 41B is incident).

  By the way, the electronic cassette 40 according to the present embodiment has a deterioration detection function for detecting a degree of deterioration indicating the degree of deterioration of the scintillator 8 caused by distortion or the like of the radiation detector 20 with respect to the radiation incident direction. .

  For this reason, in the electronic cassette 40 according to the present embodiment, as shown in FIG. 7, the conductive material for detecting the amount of distortion of the radiation detector 20 is provided at the center of the lower surface side of the scintillator 8 of the radiation detector 20. The adhesive rubber 46 and a temperature sensor 47 for detecting the temperature of the radiation detector 20 are bonded.

  As shown in FIGS. 7 and 8, the conductive rubber 46 according to the present embodiment is a rectangular column having a rectangular shape in plan view, and a pair of electrodes 46 </ b> A and 46 </ b> B are provided on a pair of side surfaces facing each other. Is provided. The electrodes 46A and 46B are bonded to the surface of the conductive rubber 46 using a conductive adhesive such as an epoxy resin.

  The conductive rubber 46 according to the present embodiment is obtained by adding a carbon material such as carbon nanofiber to a rubber material.

  The carbon material to be added is preferably carbon nanofibers, but carbon nanotubes or carbon black may be used. These carbon materials may be used alone or in combination. Since carbon nanofibers are fine, they can maintain the mechanical properties of rubber even when added to a rubber material, and exhibit the inherent strain of rubber. Moreover, cost can be reduced by using carbon nanofibers.

  The rubber material is not particularly limited. For example, rubber materials such as styrene-butadiene rubber, urethane rubber, silicone rubber, nitrile rubber, acrylic rubber, elastomer, fluorine rubber, polyethylene, polypropylene, thermoplastic elastomer, acrylonitrile. -Resin materials such as butadiene-styrene copolymer, acrylic, polyvinyl chloride, polyethylene terephthalate, polyphenylene sulfide, polyamide, polycarbonate, and polyacetal can be used.

  On the other hand, as shown in FIGS. 6 and 8, a cassette control unit 58 and a power supply unit, which will be described later, are located on one end inside the housing 41 at a position that does not overlap the radiation detector 20 (outside the range of the imaging region 41A). A case 42 for accommodating 70 (see FIG. 12 for both) is arranged.

  The casing 41 is made of, for example, carbon fiber (carbon fiber), aluminum, magnesium, bionanofiber (cellulose microfibril), or a composite material in order to reduce the weight of the entire electronic cassette 40.

  As the composite material, for example, a material including a reinforced fiber resin is used, and the reinforced fiber resin includes carbon, cellulose, and the like. Specifically, as the composite material, carbon fiber reinforced plastic (CFRP), a structure in which a foamed material is sandwiched with CFRP, or a material in which the surface of the foamed material is coated with CFRP is used. In the present embodiment, a structure in which a foam material is sandwiched with CFRP is used. Thereby, compared with the case where the housing | casing 41 is comprised with a carbon single-piece | unit, the intensity | strength (rigidity) of the housing | casing 41 can be improved.

  On the other hand, as shown in FIG. 8, a support body 44 is disposed on the inner surface of the back surface portion 41 </ b> C facing the top plate 41 </ b> B inside the housing 41, and radiation detection is performed between the support body 44 and the top plate 41 </ b> B. The vessel 20 and the lead plate 43 are arranged in this order in the irradiation direction of the radiation X.

  The support body 44 is made of, for example, a foam material from the viewpoint of weight reduction and absorption of dimensional deviation, and supports the lead plate 43.

  In addition, a ground plate 48 is attached to a position immediately below the conductive rubber 46 on the upper surface of the lead plate 43 so that the upper surface is in contact with the lower surface of the conductive rubber 46. Therefore, the conductive rubber 46 is supported on the back surface portion 41 </ b> C of the housing 41 by the ground plate 48, the lead plate 43, and the support body 44.

  In the electronic cassette 40 according to the present embodiment, the ground plate 48 is electrically connected to the housing 41 via the lead plate 43, thereby grounding the conductive rubber 46. However, the conductive rubber 46 may be grounded by electrically connecting the ground plate 48 directly to the housing 41.

  On the other hand, as shown in FIGS. 8 to 10, an adhesive member 80 is provided on the inner surface of the top plate 41 </ b> B so that the TFT substrate 30 of the radiation detector 20 can be peeled off. As the adhesive member 80, for example, a double-sided tape is used. In this case, the double-sided tape is formed so that the adhesive force of one adhesive surface is stronger than the adhesive force of the other adhesive surface.

  Specifically, the weak adhesive surface (weakly adhesive surface) is set to 1.0 N / cm or less at 180 ° peel adhesive force. Then, the surface having a strong adhesive force (strong adhesion surface) is in contact with the top plate 41B, and the weak adhesion surface is in contact with the TFT substrate 30. Thereby, compared with the case where the radiation detector 20 is fixed to the top plate 41B with fixing members, such as a screw, the thickness of the electronic cassette 40 can be made thin. Even if the top plate 41B is deformed by an impact or load, the radiation detector 20 follows the deformation of the top plate 41B having high rigidity, so that only a large curvature (slow bend) is generated, and a local low curvature is generated. Therefore, the possibility that the radiation detector 20 is damaged is reduced. Furthermore, the radiation detector 20 contributes to the improvement of the rigidity of the top plate 41B. The double-sided tape also has an adhesive force on a surface other than the surface in contact with the TFT substrate 30 and the top plate 41B.

  Further, as shown in FIG. 9, the adhesive member 80 is disposed along the side wall of the housing 41 in a state of being formed in a belt shape. Thus, an internal space B is formed between the TFT substrate 30 and the top plate 41B in a state where the TFT substrate 30 is bonded to the top plate 41B (see also FIG. 8).

  As shown in FIG. 10, the adhesive member 80 is formed with a communication path 82 that communicates the internal space B and the external space A at a portion corresponding to the corner of the top plate 41B. The communication path 82 is bent and specifically has four corners 84. That is, the communication path 82 has a labyrinth structure formed so as to be bent. In addition, the bending angle of the bent part (corner part 84) of the communication path 82 can be set arbitrarily, and may be bent like a bow. Further, the passage width d of the communication passage 82 is set as narrow as possible within a range where air can flow. However, the passage width d of the communication passage 82 may be set arbitrarily.

  As described above, in the electronic cassette 40 according to the present exemplary embodiment, the radiation detector 20 is attached to the inside of the top plate 41B of the housing 41, so that the housing 41 is on the top plate 41B side and the back surface portion 41C side. When the radiation detector 20 is attached to the top plate 41B or the radiation detector 20 is peeled off from the top plate 41B, the housing 41 is placed on the top plate 41B side. And the back surface portion 41C side are separated into two.

  In the present embodiment, the radiation detector 20 may not be bonded to the top plate 41B in a clean room or the like. This is because when a foreign object such as a metal piece that absorbs radiation is mixed between the radiation detector 20 and the top plate 41B, the foreign object can be removed by peeling the radiation detector 20 from the top plate 41B.

  By the way, when peeling the radiation detector 20 from the top plate 41B so as to directly grip the radiation detector 20, the side wall of the housing 41 becomes an obstacle. Therefore, as shown in FIG. 11, ears 86 may be provided on the TFT substrate 30 of the radiation detector 20. Thus, the operator can easily peel the radiation detector 20 from the top board 41B while holding the ear 86. The ear 86 may be fixed to the TFT substrate 30 or may be detachable from the TFT substrate 30. In the latter case, it is possible to eliminate the concern that the ear 86 becomes an obstacle when capturing a radiographic image.

  Next, with reference to FIG. 12, the configuration of the main part of the electrical system of the imaging system 104 according to the present embodiment will be described.

  As shown in the figure, the radiation detector 20 built in the electronic cassette 40 has a gate line driver 52 disposed on one side of two adjacent sides and a signal processing unit 54 disposed on the other side. Each gate wiring 34 of the TFT substrate 30 is connected to a gate line driver 52, and each data wiring 36 of the TFT substrate 30 is connected to a signal processing unit 54.

  The housing 41 includes an image memory 56, a cassette control unit 58, and a wireless communication unit 60.

  Each thin film transistor 10 of the TFT substrate 30 is sequentially turned on in a row unit by a signal supplied from the gate line driver 52 via the gate wiring 34, and the electric charge read by the thin film transistor 10 in the on state is converted into an electric signal. The data wiring 36 is transmitted and input to the signal processing unit 54. As a result, the charges are sequentially read out in units of rows, and a two-dimensional radiation image can be acquired.

  Although not shown, the signal processing unit 54 includes an amplification circuit and a sample hold circuit for amplifying an input electric signal for each data wiring 36, and the electric signal transmitted through the individual data wiring 36. Is amplified by the amplifier circuit and then held in the sample hold circuit. Further, a multiplexer and an A / D (analog / digital) converter are connected in order to the output side of the sample and hold circuit, and the electric signals held in the individual sample and hold circuits are sequentially (serially) input to the multiplexer. The digital image data is converted by an A / D converter.

  An image memory 56 is connected to the signal processing unit 54, and image data output from the A / D converter of the signal processing unit 54 is sequentially stored in the image memory 56. The image memory 56 has a storage capacity capable of storing a predetermined number of image data, and image data obtained by imaging is sequentially stored in the image memory 56 each time a radiographic image is captured.

  The image memory 56 is connected to the cassette control unit 58. The cassette control unit 58 includes a microcomputer, and includes a CPU (Central Processing Unit) 58A, a memory 58B including a ROM (Read Only Memory) and a RAM (Random Access Memory), a nonvolatile storage unit 58C including a flash memory and the like. And controls the entire operation of the electronic cassette 40.

  The cassette control unit 58 is connected to electrodes 46A and 46B of the conductive rubber 46, applies a predetermined voltage between the electrodes 46A and 46B, and based on the current value at this time, the conductive rubber 46. A resistance measurement unit 58D for measuring the resistance value of the radiation detector is provided, and the cassette control unit 58 is based on the resistance value measured by the resistance measurement unit 58D (hereinafter referred to as “measurement resistance value”). The amount of strain at the location where the 20 conductive rubbers 46 are disposed can be grasped. In the electronic cassette 40 according to the present embodiment, information indicating the relationship between the measured resistance value and the amount of distortion is based on an experiment using a real machine of the same type as the electronic cassette 40 or a design specification of the electronic cassette 40. The distortion amount is obtained in advance by computer simulation or the like, and the distortion amount is derived using the information.

  In addition, the cassette control unit 58 is provided with a time measuring unit 58E that measures the elapsed time, and the cassette control unit 58 can control the operation of the time measuring unit 58E and the time measured by the time measuring unit 58E. Can be grasped.

  Further, a temperature sensor 47 is connected to the cassette control unit 58, and the cassette control unit 58 can grasp the temperature at the location where the temperature sensor 47 is disposed.

  Further, a wireless communication unit 60 is connected to the cassette control unit 58. The wireless communication unit 60 corresponds to a wireless local area network (LAN) standard represented by IEEE (Institute of Electrical and Electronics Engineers) 802.11a / b / g / n, etc. Control the transmission of various information between them. The cassette control unit 58 can wirelessly communicate with an external device such as the console 110 that performs control related to radiographic image capturing via the wireless communication unit 60, and can transmit and receive various types of information to and from the console 110 and the like. It is possible.

  The electronic cassette 40 is provided with a power supply unit 70, which functions as the above-described various circuits and elements (gate line driver 52, signal processing unit 54, image memory 56, wireless communication unit 60, and cassette control unit 58). The microcomputer or the like) is operated by the power supplied from the power supply unit 70. The power supply unit 70 incorporates a battery (a rechargeable secondary battery) so as not to impair the portability of the electronic cassette 40, and supplies power from the charged battery to various circuits and elements. In FIG. 12, wiring for connecting the power supply unit 70 to various circuits and elements is omitted.

  On the other hand, the console 110 is configured as a server computer, and includes a display 111 that displays an operation menu, a captured radiographic image, and the like, and a plurality of keys, and inputs various information and operation instructions. An operation panel 112.

  The console 110 according to the present embodiment includes a CPU 113 that controls the operation of the entire apparatus, a ROM 114 that stores various programs including a control program in advance, a RAM 115 that temporarily stores various data, and various data. An HDD (Hard Disk Drive) 116 that stores and holds, a display driver 117 that controls display of various types of information on the display 111, and an operation input detection unit 118 that detects an operation state of the operation panel 112 are provided. . In addition, the console 110 transmits and receives various types of information such as an exposure condition, which will be described later, to and from the radiation generation apparatus 120 through wireless communication, and transmits and receives various types of information such as image data to and from the electronic cassette 40. A wireless communication unit 119 is provided.

  The CPU 113, ROM 114, RAM 115, HDD 116, display driver 117, operation input detection unit 118, and wireless communication unit 119 are connected to each other via the system bus BUS. Therefore, the CPU 113 can access the ROM 114, RAM 115, and HDD 116, controls the display of various information on the display 111 via the display driver 117, and the radiation generator 120 via the wireless communication unit 119 and Control of transmission and reception of various types of information with the electronic cassette 40 can be performed. Further, the CPU 113 can grasp the operation state of the user with respect to the operation panel 112 via the operation input detection unit 118.

  On the other hand, the radiation generator 120 includes a radio communication unit 123 that transmits and receives various types of information such as an exposure condition between the radiation source 121 and the console 110, and a line that controls the radiation source 121 based on the received exposure condition. A source control unit 122.

  The radiation source control unit 122 is also configured to include a microcomputer, and stores the received exposure conditions and the like. The exposure conditions received from the console 110 include information such as tube voltage, tube current, and exposure period. The radiation source control unit 122 causes the radiation source 121 to emit radiation X based on the received exposure conditions.

  By the way, as described above, the electronic cassette 40 according to the present embodiment detects a deterioration level indicating the degree of deterioration of the scintillator 8 caused by the distortion of the radiation detector 20 with respect to the radiation incident direction. have. For this reason, in the electronic cassette 40 according to the present exemplary embodiment, three types of information including distortion deterioration coefficient information, time deterioration coefficient information, and temperature deterioration coefficient information illustrated in FIG. 13 are stored in advance in the ROM of the memory 58B. ing.

  As shown in FIG. 13A, the distortion deterioration coefficient information according to the present embodiment is configured by previously storing deterioration coefficients for each predetermined distortion amount range. As shown in FIG. 13, the time degradation coefficient information according to the present embodiment is configured by previously storing a degradation coefficient for each predetermined time range. As illustrated in FIG. The temperature deterioration coefficient information according to is configured by storing in advance a deterioration coefficient for each predetermined temperature range.

  Next, the operation of the imaging system 104 according to the present embodiment will be described.

  First, with reference to FIG. 14, the operation of the console 110 when radiographic images are taken will be described. FIG. 14 is a flowchart showing a flow of processing of the radiographic image capturing processing program executed by the CPU 113 of the console 110 at this time, and the program is stored in a predetermined area of the ROM 114 in advance.

  In step 300 in the figure, the display driver 117 is controlled so that a predetermined initial information input screen is displayed on the display 111, and in step 302, input of predetermined information is waited.

  FIG. 15 shows an example of an initial information input screen displayed on the display 111 by the process of step 300 described above. As shown in the figure, in the initial information input screen according to the present embodiment, the name of the subject who is going to capture a radiographic image, the region to be imaged, and the posture at the time of capturing (in this embodiment, lying down, standing , And a message prompting the user to input radiation X exposure conditions at the time of imaging (in this embodiment, tube voltage, tube current, and exposure period when radiation X is exposed), and these The information input area is displayed.

  When the initial information input screen shown in the figure is displayed on the display 111, the photographer can input the name of the subject to be imaged, the imaging region, the posture at the time of imaging, and the exposure conditions corresponding to each of the input areas. Is input via the operation panel 112.

  When the posture at the time of imaging is the standing position or the lying position, the photographer holds the electronic cassette 40 in the holding section 162 of the corresponding standing table 160 or the holding section 166 of the lying table 164 and also the radiation source. After positioning 121 at the corresponding position, the subject is positioned at a predetermined imaging position. On the other hand, when a radiographic image is taken in a state where the imaging part does not hold the electronic cassette 40 such as an arm part or a leg part in the holding part, the photographer is ready to take a picture of the imaging part. The electronic cassette 40 and the radiation source 121 are positioned. Thereafter, the photographer designates an end button displayed near the lower end of the initial information input screen via the operation panel 112. When an end button is designated by the photographer, step 302 is affirmative and the process proceeds to step 304.

  In step 304, an instruction to instruct the electronic cassette 40 to transmit a later-described cumulative deterioration degree stored in the storage unit 58C at this time by executing a deterioration degree deriving process (see also FIG. 16) described later. After the information is transmitted to the electronic cassette 40 via the wireless communication unit 119, in the next step 306, reception of the cumulative deterioration level is waited. In response to this, the electronic cassette 40 reads the cumulative deterioration degree from the storage unit 58C and transmits it to the console 110 via the wireless communication unit 60. In response to this, step 306 is affirmative and the process proceeds to step 308.

  In step 308, the radiation after the current imaging is performed based on the cumulative deterioration degree received from the electronic cassette 40 and the information input on the initial information input screen (hereinafter referred to as "initial information"). A predicted value of the deterioration level of the detector 20 (hereinafter referred to as “deterioration level predicted value”) is derived as follows.

  First, the degree of deterioration that progresses in the radiation detector 20 by the current imaging is predicted according to the imaging region included in the initial information and the posture at the time of imaging. In the present embodiment, it is assumed that the radiation detector 20 receives the prediction by one imaging for each of all combinations of imaging regions to be applied in the imaging system 104 and postures at the time of imaging. The degree of deterioration (hereinafter referred to as “assumed degree of deterioration”) is stored in advance in storage means such as the HDD 116, and the assumed degree of deterioration corresponding to the imaging region and the posture at the time of imaging included in the initial information is stored in the storage means. This is done by reading from. Here, in the present embodiment, as the assumed deterioration degree, an experiment using a real machine of the same type as the electronic cassette 40 or a design specification of the electronic cassette 40 is used for each combination of the imaging region and the posture at the time of imaging. A value obtained in advance by computer simulation or the like according to the above is applied.

  Then, the deterioration degree predicted value is calculated by adding the deterioration degree predicted as described above to the cumulative deterioration degree received from the electronic cassette 40.

  In the next step 310, it is determined whether or not the predicted deterioration level derived by the processing in step 308 is smaller than a predetermined first threshold value. If the determination is negative, the process proceeds to step 312. In the present embodiment, a value preset by a photographer or the like is applied as the first threshold value. However, the first threshold value is not limited to this, and a value or the like predetermined according to the use of the electronic cassette 40 or the like. It goes without saying that may be applied.

  In step 312, a predetermined warning process is executed, and then the radiation image capturing process program is terminated. In the present embodiment, as the warning process, the display 111 displays information indicating that the current imaging by the electronic cassette 40 cannot be performed because the radiation detector 20 has deteriorated, and the derived deterioration degree prediction value. Although the processing is applied, the present invention is not limited to this, processing for generating a sound indicating a warning using a sound generating device such as a speaker built in the console 110, and information indicating a warning to an external device such as the RIS server 150 You may apply the process which performs other warnings, such as the process to transmit, individually or in combination.

  On the other hand, if an affirmative determination is made in step 310, the process proceeds to step 314, where the exposure condition is set by transmitting the exposure condition included in the initial information to the radiation generator 120 via the wireless communication unit 119. To do. In response to this, the radiation source control unit 122 of the radiation generator 120 prepares for exposure under the received exposure conditions.

  In the next step 316, instruction information for instructing the start of exposure is transmitted to the radiation generator 120 and the electronic cassette 40 via the wireless communication unit 119.

  In response to this, the radiation source 121 generates and emits radiation X at a tube voltage, a tube current, and an exposure period corresponding to the exposure conditions received by the radiation generator 120 from the console 110. The radiation X exposed from the radiation source 121 reaches the electronic cassette 40 after passing through the subject.

  On the other hand, when the cassette control unit 58 of the electronic cassette 40 receives the instruction information instructing the start of exposure, the cassette control unit 58 starts accumulating charges in the capacitors 9 of the respective pixel units 32 of the built-in radiation detector 20. After the elapse of the exposure period specified by the exposure condition, the gate line driver 52 is controlled to output an ON signal to each gate wiring 34 one line at a time from the gate line driver 52, and each gate line 34 connected to each gate wiring 34. The thin film transistors 10 are sequentially turned on line by line.

  In the radiation detector 20, when the thin film transistors 10 connected to the gate lines 34 are turned on line by line, the charges accumulated in the capacitors 9 line by line flow out to the data lines 36 as electric signals. The electric signal flowing out to each data wiring 36 is converted into digital image data by the signal processing unit 54 and stored in the image memory 56.

  The cassette control unit 58 transmits the image data stored in the image memory 56 to the console 110 by wireless communication after the end of photographing. At this time, the cassette control unit 58 may execute a later-described deterioration degree derivation process (see also FIG. 16) and transmit the cumulative deterioration degree of the radiation detector 20 obtained thereby to the console 110. .

  Therefore, in the next step 318, the process waits until the image data is received from the electronic cassette 40. In the next step 320, it is determined whether or not the cumulative deterioration level is received from the electronic cassette 40, and a negative determination is made. If YES, the process proceeds to step 326 described later. If YES is determined, the process proceeds to step 322.

  In step 322, it is determined whether or not the cumulative deterioration level received from the electronic cassette 40 is smaller than the first threshold value. If the determination is affirmative, the process proceeds to step 326 described later. Goes to step 324.

  In step 324, a predetermined warning process is executed, and then the process proceeds to step 326. In the present embodiment, as the warning process, the display 111 displays information indicating that the radio cassette 20 has deteriorated, and thus the electronic cassette 40 cannot perform the next imaging, and the received cumulative deterioration level. Although the processing is applied, the present invention is not limited to this, processing for generating a sound indicating a warning using a sound generating device such as a speaker built in the console 110, and information indicating a warning to an external device such as the RIS server 150 You may apply the process which performs other warnings, such as the process to transmit, individually or in combination.

  In step 326, image processing for performing various corrections such as shading correction on the image data received by the processing in step 318 is executed.

  In the next step 328, the image data subjected to the image processing (hereinafter referred to as “corrected image data”) is stored in the HDD 116, and in the next step 330, the radiation image indicated by the corrected image data is stored. The display driver 117 is controlled so as to be displayed on the display 111 for confirmation, etc., and in the next step 332, the corrected image data is transmitted to the RIS server 150 via the in-hospital network 102, and then the radiographic imaging is performed. Terminate the processing program. Note that the corrected image data transmitted to the RIS server 150 is stored in the database 150A, so that the doctor can perform interpretation, diagnosis, and the like of the radiographic image taken.

  Next, with reference to FIG. 16, the operation of the electronic cassette 40 when executing the deterioration degree derivation process will be described. Note that FIG. 16 is executed by the CPU 58A of the electronic cassette 40 in parallel with the above-described imaging operation when the instruction information instructing the start of exposure transmitted by the process of step 316 of the radiographic image capturing processing program is received. The deterioration degree deriving process program is a flowchart showing the process flow, and the program is stored in advance in a predetermined area of the memory 58B.

  In step 400 of the figure, the resistance value of the conductive rubber 46 at this time is measured by the resistance measuring unit 58D, and in the next step 402, the strain amount of the radiation detector 20 is calculated based on the measured resistance value. Derived by the method.

  In the next step 404, it is determined whether or not the amount of distortion derived by the processing in step 402 is equal to or greater than a predetermined second threshold value (1 mm in the present embodiment). Control goes to step 406. In the present embodiment, an actual machine of the same type as the electronic cassette 40 is used as the second threshold value, which can be regarded as a deterioration of the radiation detector 20 when the distortion amount exceeds the value. Values obtained in advance by computer simulation or the like according to the experiment used or the design specifications of the electronic cassette 40 are applied.

  In step 406, it is determined whether or not the photographing operation has been completed. If a negative determination is made, the process returns to step 400. If an affirmative determination is made, the deterioration degree derivation processing program is ended.

  On the other hand, if the determination in step 404 is affirmative, the process proceeds to step 408, where the time measuring unit 58E built in the cassette control unit 58 starts measuring, and in the next step 410, the conductive rubber 46 at this time is started. The resistance value and the temperature of the radiation detector 20 are measured by the resistance measuring unit 58D and the temperature sensor 47.

  In the next step 412, the distortion amount of the radiation detector 20 is derived by the above-described method based on the resistance value measured by the processing in the above step 410. In the next step 414, the derived distortion amount and the above step 410 are derived. The temperature measured by the process is stored in a predetermined area of the storage unit 58C.

  In the next step 416, it is determined whether or not the amount of distortion derived by the processing in step 412 has become smaller than the second threshold value. If a negative determination is made, the process returns to step 410, but an affirmative determination is made. At this point, the process proceeds to step 418.

  In step 418, the time measurement by the time measuring unit 58E started by the processing of step 408 is stopped, and in the next step 420, the above-described distortion deterioration coefficient information, time deterioration coefficient information, and temperature deterioration coefficient information, and the accumulation described later. The degree of deterioration is read from the memory 58B and the storage unit 58C.

  In the next step 422, the distortion deterioration coefficient information, the time deterioration coefficient information, the temperature deterioration coefficient information, and the cumulative deterioration degree read by the process of step 420, the distortion amount stored in the storage unit 58C by the process of step 414, and Based on the temperature and the time measured by the time measuring unit 58E, the cumulative deterioration degree of the radiation detector 20 is derived as follows.

  First, the degree of degradation r received by the radiation detector 20 by the current imaging is calculated by the following equation (1).

  In the equation (1), Hvc represents a deterioration coefficient corresponding to the strain amount (in this embodiment, the maximum value of the strain amount stored by the processing in step 414), and Tpc is the temperature (in this embodiment). , The deterioration coefficient corresponding to the time measured by the timer 58E, and the deterioration coefficient corresponding to the time measured by the timer 58E.

  Next, the cumulative deterioration degree R ′ is calculated by the equation (2). In the equation (2), R represents the cumulative deterioration level up to the previous shooting. Here, when the current shooting is the first shooting by the electronic cassette 40, there is no cumulative deterioration level R until the previous shooting, and in this case, the cumulative deterioration level R is set to 0 (zero). Apply.

  In the next step 424, the cumulative deterioration level R ′ obtained by the processing in step 422 is stored (overwritten) in a predetermined area of the storage unit 58C. Note that the accumulated deterioration degree stored here is read out and used when performing calculations according to the expressions (1) and (2) at the next photographing.

  In the next step 426, the cumulative deterioration level R 'is transmitted to the console 110 via the wireless communication unit 60, and then the deterioration level derivation processing program is terminated.

  Incidentally, in the electronic cassette 40 according to the present embodiment, as shown in FIG. 8, the radiation detector 20 is incorporated so that the radiation X is irradiated from the TFT substrate 30 side.

  Here, as shown in FIG. 17, the radiation detector 20 is irradiated with radiation from the side on which the scintillator 8 is formed, and reads a radiation image by the TFT substrate 30 provided on the back side of the incident surface of the radiation. In the case of a so-called back surface reading method, light is emitted more strongly on the upper surface side of the scintillator 8 (opposite side of the TFT substrate 30), and radiation is irradiated from the TFT substrate 30 side. In the case of a so-called surface reading method in which a radiation image is read by the TFT substrate 30 provided on the TFT substrate 30, the radiation transmitted through the TFT substrate 30 enters the scintillator 8 and the TFT substrate 30 side of the scintillator 8 emits light more strongly. Electric charges are generated in each sensor unit 13 provided on the TFT substrate 30 by light generated by the scintillator 8. For this reason, since the radiation detector 20 is closer to the light emission position of the scintillator 8 with respect to the TFT substrate 30 when the front surface reading method is used than when the rear surface reading method is used, the resolution of the radiation image obtained by imaging is higher. high.

  In the radiation detector 20, the photoelectric conversion film 4 is made of an organic photoelectric conversion material, and the photoelectric conversion film 4 hardly absorbs radiation. For this reason, the radiation detector 20 according to the present embodiment suppresses a decrease in sensitivity to radiation because the amount of radiation absorbed by the photoelectric conversion film 4 is small even when radiation is transmitted through the TFT substrate 30 by the surface reading method. Can do. In the surface reading method, radiation passes through the TFT substrate 30 and reaches the scintillator 8. Thus, when the photoelectric conversion film 4 of the TFT substrate 30 is made of an organic photoelectric conversion material, the radiation in the photoelectric conversion film 4 is obtained. Therefore, it is suitable for the surface reading method.

  In addition, both the amorphous oxide constituting the active layer 17 of the thin film transistor 10 and the organic photoelectric conversion material constituting the photoelectric conversion film 4 can be formed at a low temperature. For this reason, the board | substrate 1 can be formed with a plastic resin, aramid, and bio-nanofiber with little radiation absorption. Since the substrate 1 formed in this way has a small amount of radiation absorption, even when the radiation passes through the TFT substrate 30 by the surface reading method, it is possible to suppress a decrease in sensitivity to radiation.

  Further, according to the present embodiment, as shown in FIG. 8, the radiation detector 20 is attached to the top plate 41B in the casing 41 so that the TFT substrate 30 is on the top plate 41B side. When 1 is formed of a highly rigid plastic resin, aramid, or bio-nanofiber, the radiation detector 20 itself has high rigidity, so that the top plate 41B of the housing 41 can be formed thin. In addition, when the substrate 1 is formed of a highly rigid plastic resin, aramid, or bionanofiber, the radiation detector 20 itself has flexibility, so that even when an impact is applied to the imaging region 41A, the radiation detector 20 is damaged. It ’s hard.

  As described above in detail, in the present embodiment, the top plate of the housing 41 is placed on the surface of the radiation detector 20 attached to the top plate 41B opposite to the surface attached to the top plate 41B. Since the conductive rubber 46 supported on the surface opposite to 41B is attached, the vibration of the radiation detector 20 generated when the electronic cassette 40 is carried can be suppressed. As a result, the radiation caused by the vibration Charge of the detector 20 can be prevented.

  In the present embodiment, since the conductive rubber 46 is grounded, static electricity generated in the radiation detector 20 can be effectively discharged.

  In the present embodiment, since the conductive rubber 46 is attached to the center of the surface opposite to the surface attached to the top plate 41B of the radiation detector 20, static electricity generated in the radiation detector 20 is obtained. Can be discharged more effectively.

  Further, in the present embodiment, the radiation detector 20 includes a scintillator 8 that generates light when irradiated with radiation, and an organic photoelectric conversion material that generates charges when receiving light generated by the scintillator 8. Therefore, the impact resistance of the electronic cassette 40 can be improved.

  Further, in the present embodiment, since the top plate 41B is made of a material containing reinforcing fiber resin, it is possible to increase the strength of the top plate as compared with the case where the top plate is made of carbon alone or the like. it can.

  In particular, in the present embodiment, since the reinforcing fiber resin is carbon fiber reinforced plastic, it is possible to increase the thermal conductivity of the top plate 41B compared to the case where the top plate 41B is made of carbon alone or the like. As a result, image unevenness due to temperature unevenness of the radiation image obtained by the radiation detector 20 can be suppressed.

  In the present embodiment, the resistance value of the conductive rubber 46 is detected, and the amount of distortion of the radiation detector 20 is derived based on the detected resistance value. Therefore, the radiation detector is used using the derived amount of distortion. The state of 20 deterioration can be grasped, and countermeasures according to the state of deterioration can be taken.

  Moreover, in this Embodiment, since the radiation detector 20 is attached to the top plate 41B so that separation | spacing is possible, replacement | exchange of a housing | casing can be performed efficiently.

  In the present embodiment, since the internal space B is formed between the TFT substrate 30 and the top plate 41B, when the radiation detector 20 is bonded to the top plate 41B, the TFT substrate 30 and the top plate 41B are bonded. Even if air remains on the bonding surface of the member 80, the remaining air can escape to the internal space B. In addition, since the communication member 82 that communicates the internal space B and the external space A is formed in the adhesive member 80, the pressure in the internal space B and the air pressure in the external space A can be reduced even when the atmospheric pressure in the external space A changes. Can be kept constant. Thereby, it can prevent that the adhesiveness of the TFT substrate 30 with respect to the top plate 41B falls by atmospheric pressure change.

  In the present embodiment, the communication path 82 has a corner 84. Therefore, even when foreign matter having a mass larger than that of air flows into the communication path 82 from the external space A, the foreign matter cannot follow the flow of air flowing through the corner portion 84. Mixing into B can be prevented. As a result, it is possible to suppress contamination of foreign matter that leads to deterioration of the quality of the radiation image.

  Further, since the communication path 82 is formed in the adhesive member 80 and the adhesive member 80 has adhesive force on the entire surface, the foreign matter that could not follow the air adheres to the wall surface of the communication path 82 at the corner 84. It becomes easy. Therefore, the foreign matter can be reliably captured in the communication path 82. Therefore, it is possible to more reliably prevent foreign matter from entering the internal space B.

  Further, according to the present embodiment, the passage width d of the communication passage 82 is set as narrow as possible within the range in which air can circulate, so that it is possible to cope with the mixing of foreign matters such as relatively small metal powder. it can. If the passage width d of the communication passage 82 is set according to the assumed size of the foreign matter, it is possible to efficiently prevent the foreign matter from being mixed.

  By the way, generally, the scintillator 8 is more fragile than the TFT substrate 30. Therefore, when the scintillator 8 is bonded to the top plate 41B with the adhesive member 80, the scintillator 8 may be damaged when the radiation detector 20 is peeled off. However, in the present embodiment, since the TFT substrate 30 is bonded to the top plate 41B with the adhesive member 80, the concern that the scintillator 8 is damaged when the radiation detector 20 is peeled can be eliminated.

  Depending on the shooting environment, shooting may be performed with a subject (patient) on the top board 41B. In this case, the top plate 41B is easily damaged. When the top plate 41B is scratched, it may be displayed on the radiographic image as fixed pattern noise, so it is desirable to replace the housing 41. However, when the radiation detector 20 is pasted to the top plate 41B so as not to be peeled off, there is a problem that when the casing 41 is replaced, the expensive radiation detector 20 needs to be replaced together and costs increase. It was. According to the present embodiment, since the radiation detector 20 is detachably bonded to the top plate 41B, the housing 41 can be efficiently replaced.

  As mentioned above, although this invention was demonstrated using embodiment, the technical scope of this invention is not limited to the range as described in the said embodiment. Various modifications or improvements can be added to the above-described embodiment without departing from the gist of the invention, and embodiments to which such modifications or improvements are added are also included in the technical scope of the present invention.

  The above embodiments do not limit the invention according to the claims (claims), and all the combinations of features described in the embodiments are essential for the solution means of the invention. Is not limited. The embodiments described above include inventions at various stages, and various inventions can be extracted by appropriately combining a plurality of disclosed constituent elements. Even if some constituent requirements are deleted from all the constituent requirements shown in the embodiment, as long as an effect is obtained, a configuration from which these some constituent requirements are deleted can be extracted as an invention.

  For example, in the above embodiment, the case where the conductive rubber 46 is supported on the back surface portion 41C of the housing 41 with the ground plate 48 interposed is described, but the present invention is not limited to this. The conductive rubber 46 may be supported on the back surface portion 41 </ b> C of the housing 41 without interposing the ground plate 48.

  Moreover, although the said embodiment demonstrated the case where the shape of the conductive rubber 46 was a square pillar shape, this invention is not limited to this, For example, cylindrical shape, multiple square pillar shapes other than a square, etc. It is good also as a form made into another shape.

  Moreover, in the said embodiment, although it did not mention about the foaming presence or absence of the conductive rubber 46, the conductive rubber 46 may have a foaming property. Thereby, the anti-vibration property with respect to a radiation detector can be improved more.

  In the above embodiment, the case where the conductive rubber 46 is grounded has been described. However, the present invention is not limited to this, and the conductive rubber 46 may not be grounded. In this case, although the static electricity charged in the radiation detector 20 cannot be discharged, the vibration of the radiation detector 20 when carrying the electronic cassette 40 can be suppressed, so that a certain amount of static electricity is prevented. The effect to do is obtained.

  In the above embodiment, the case where the conductive rubber 46 is provided in the central portion of the radiation detector 20 has been described. However, the present invention is not limited to this. For example, the conductive rubber 46 is detected by radiation. It is good also as a form provided in other positions except the center part in the container 20. FIG.

  In the above embodiment, the case where only one conductive rubber 46 is provided in the radiation detector 20 has been described. However, the present invention is not limited to this. For example, a plurality of conductive rubbers 46 are provided. It is good also as a form which each provides in the position where the radiation detector 20 differs.

  In this case, the conductive rubber 46 may be provided in the central portion of the scintillator 8 as in the above embodiment, while another conductive rubber may be provided in the peripheral portion of the scintillator 8.

  In this case, the conductive rubber 46 provided in the central portion of the scintillator 8 is used to derive the amount of distortion of the radiation detector 20 from the resistance value as in the above embodiment, and provided in the peripheral portion of the scintillator 8. It is good also as a form grounded with conductive rubber.

  Further, in this case, a plurality of conductive rubbers may be provided in the periphery of the scintillator 8 and a part of them may be used as a wireless LAN communication antenna. As a particularly preferable form in this case, as shown in FIG. 19 as an example, one conductive rubber 46 is provided in the central portion of the scintillator 8, while four conductive rubbers 46 a to 46 d are provided in the peripheral portion of the scintillator 8. In addition, two of the four conductive rubbers 46a to 46d are used as antennas for wireless communication such as diversity communication, and at least one of the conductive rubbers 46a to 46d is used for grounding. be able to.

  In the above embodiment, the case where the warning process is executed by the console 110 when the predicted deterioration level and the cumulative deterioration level are equal to or greater than a predetermined threshold has been described. However, the present invention is not limited to this. Instead, the warning process may be executed in the electronic cassette 40. In this case, the CPU 58 </ b> A of the electronic cassette 40 executes the processes of Step 308 to Step 312, Step 322, and Step 324 of the radiographic imaging process program.

  In the above embodiment, the case where the sensor unit 13 is configured to include an organic photoelectric conversion material that generates charges by receiving light generated by the scintillator 8 has been described. It is not limited, It is good also as a form which applies what was comprised without including an organic photoelectric conversion material as the sensor part 13. FIG.

  In the above embodiment, the case has been described in which the degree of deterioration is derived using all of the distortion deterioration coefficient information, the time deterioration coefficient information, and the temperature deterioration coefficient information shown in FIG. 13, but the present invention is not limited to this. Instead, the distortion deterioration coefficient information may be used alone, or the distortion deterioration coefficient information may be combined with any one of the time deterioration coefficient information and the temperature deterioration coefficient information.

  In the above-described embodiment, the case where the use of the electronic cassette 40 is prohibited when the deterioration prediction value is equal to or greater than the first threshold when performing shooting is described. However, the present invention is not limited to this. For example, when the deterioration degree predicted value is equal to or greater than the first threshold, the use of another electronic cassette 40 having a deterioration degree predicted value that is a value at which the above imaging can be performed may be promoted.

  In the above embodiment, the case where the cumulative degradation level R ′ is applied as information indicating the degree of degradation of the radiation detector 20 has been described. However, the present invention is not limited to this, and for example, cumulative degradation is performed. Instead of the degree R ′, the deterioration degree r may be applied.

  In the above embodiment, the case where the degree of deterioration of the radiation detector 20 is derived by the electronic cassette 40 has been described. However, the present invention is not limited to this, and the degree of deterioration is derived by the console 110. It is good also as a form to do. As an example of this case, the electronic cassette 40 transmits the measurement results obtained by the resistance measurement unit 58D and the temperature sensor 47 to the console 110, and the console 110 performs steps 400, 410, and 426 in the deterioration degree derivation processing program. An example of executing the process excluding the above can be illustrated. In this case, the load due to the electronic cassette 40 can be reduced as compared with the above embodiment.

  Moreover, although the said embodiment demonstrated the case where the corner | angular part 84 was provided with two or more in the communicating path 82, this invention is not limited to this, As shown in FIG. Only one corner 92 may be provided. Thereby, the communication path 90 can be easily formed in the adhesive member 80.

  Further, when the radiation detector 20 is peeled from the top plate 41B, an organic solvent or the like may be poured into the adhesive member 80 to weaken the adhesiveness of the adhesive member 80 and then the radiation detector 20 may be peeled off. In this case, since the adhesive member 80 has corners, the organic solvent can easily penetrate into the adhesive member 80.

  Moreover, although the said embodiment demonstrated the case where it arrange | positions so that the case 42 which accommodates the cassette control part 58 and the power supply part 70 in the inside of the housing | casing 41 of the electronic cassette 40, and the radiation detector 20 may not overlap. It is not limited to this. For example, the radiation detector 20 and the cassette control unit 58 or the power supply unit 70 may be arranged so as to overlap each other.

  Moreover, although the said embodiment demonstrated the case where it communicated by radio | wireless between the electronic cassette 40 and the console 110, and between the radiation generator 120 and the console 110, this invention is limited to this. For example, at least one of these may be configured to perform wired communication.

  In the above embodiment, the case where X-rays are applied as radiation has been described. However, the present invention is not limited to this, and other radiation such as γ-rays may be applied.

  In addition, the configuration of the RIS 100 described in the above embodiment (see FIG. 1), the configuration of the radiation imaging room (see FIG. 2), the configuration of the electronic cassette 40 (see FIGS. 3 to 11), and the imaging system 104. The configuration (see FIG. 12) is an example, and an unnecessary part can be deleted, a new part can be added, or the connection state can be changed without departing from the gist of the present invention. Needless to say.

  The configuration of various information described in the above embodiment (see FIG. 13) is also an example, and unnecessary information is deleted or new information is added without departing from the gist of the present invention. It goes without saying that you can do it.

  The processing flow of various programs described in the above embodiment (see FIGS. 14 and 16) is also an example, and unnecessary steps may be deleted or new within the scope of the gist of the present invention. It goes without saying that steps can be added and the processing order can be changed.

  Furthermore, it is needless to say that each of the arithmetic expressions (1) and (2) described in the above embodiment is an example, and may be changed as appropriate without departing from the gist of the present invention.

DESCRIPTION OF SYMBOLS 1 Board | substrate 8 Scintillator 10 Thin-film transistor 13 Sensor part 20 Radiation detector 30 TFT board 40 Electronic cassette 41 Case 41A Imaging | photography area 41B Top plate 41C Back surface part 43 Lead plate 44 Support body (support member)
46 Conductive rubber 46A, 46B Electrode 47 Temperature sensor 48 Ground plate 58 Cassette control unit (leading means)
58A CPU
58D Resistance measurement unit (detection means)
58E Timekeeping unit 60 Wireless communication unit 80 Adhesive member 82 Communication path 84 Corner 90 Communication path 92 Corner 100 RIS
110 Console 111 Display 112 Operation Panel 113 CPU
116 HDD
119 Wireless communication unit 120 Radiation generator X Radiation

Claims (10)

A housing having a top plate irradiated with radiation emitted from a radiation source and transmitted through the subject;
A flat radiation detector that is provided inside the casing in a state of being attached to the top plate and that captures a radiographic image indicated by radiation transmitted through the top plate;
Conductive rubber attached to a surface opposite to the surface attached to the top plate of the radiation detector;
A support member for supporting the conductive rubber on a surface of the casing opposite to the top plate;
A radiographic imaging apparatus comprising: The radiographic imaging apparatus according to claim 1, wherein the conductive rubber is grounded. The radiographic imaging apparatus according to claim 1, wherein the conductive rubber is attached to a central portion of a surface opposite to a surface attached to the top plate of the radiation detector. The radiographic imaging apparatus according to any one of claims 1 to 3, wherein the conductive rubber has foaming properties. The radiation detector includes a sensor unit configured to include a scintillator that generates light when irradiated with radiation, and an organic photoelectric conversion material that generates charges when receiving light generated by the scintillator. The radiographic imaging device according to any one of claims 1 to 4. The radiographic image capturing apparatus according to any one of claims 1 to 5, wherein the radiation detector is detachably attached to the top plate. An adhesive member that bonds the radiation detector to the top plate so that an internal space is formed between the radiation detector and the top plate;
Ventilating means for communicating the internal space and the outside, and preventing foreign matter from entering the internal space from the outside,
The radiographic imaging device according to any one of claims 1 to 6, further comprising: The radiographic imaging device according to any one of claims 1 to 7, wherein the top plate is made of a material containing a reinforcing fiber resin. The radiographic imaging apparatus according to claim 8, wherein the reinforcing fiber resin is a carbon fiber reinforced plastic. Detecting means for detecting a resistance value of the conductive rubber;
Derivation means for deriving the amount of distortion of the radiation detector based on the resistance value detected by the detection means;
The radiographic imaging apparatus according to claim 1, further comprising:

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