WO2007096967A1 - 放射線検出器 - Google Patents
放射線検出器 Download PDFInfo
- Publication number
- WO2007096967A1 WO2007096967A1 PCT/JP2006/303275 JP2006303275W WO2007096967A1 WO 2007096967 A1 WO2007096967 A1 WO 2007096967A1 JP 2006303275 W JP2006303275 W JP 2006303275W WO 2007096967 A1 WO2007096967 A1 WO 2007096967A1
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- WO
- WIPO (PCT)
- Prior art keywords
- radiation
- semiconductor
- common electrode
- radiation detector
- pedestal
- Prior art date
Links
- 230000005855 radiation Effects 0.000 title claims abstract description 197
- 239000004065 semiconductor Substances 0.000 claims abstract description 133
- NJPPVKZQTLUDBO-UHFFFAOYSA-N novaluron Chemical compound C1=C(Cl)C(OC(F)(F)C(OC(F)(F)F)F)=CC=C1NC(=O)NC(=O)C1=C(F)C=CC=C1F NJPPVKZQTLUDBO-UHFFFAOYSA-N 0.000 claims abstract description 89
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 claims abstract description 60
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- 150000001340 alkali metals Chemical class 0.000 claims description 6
- 229940065287 selenium compound Drugs 0.000 claims description 6
- 150000003343 selenium compounds Chemical class 0.000 claims description 6
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- RZVAJINKPMORJF-UHFFFAOYSA-N Acetaminophen Chemical compound CC(=O)NC1=CC=C(O)C=C1 RZVAJINKPMORJF-UHFFFAOYSA-N 0.000 description 1
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- 239000003513 alkali Substances 0.000 description 1
- UHYPYGJEEGLRJD-UHFFFAOYSA-N cadmium(2+);selenium(2-) Chemical compound [Se-2].[Cd+2] UHYPYGJEEGLRJD-UHFFFAOYSA-N 0.000 description 1
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Classifications
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L31/00—Semiconductor devices sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation; Processes or apparatus specially adapted for the manufacture or treatment thereof or of parts thereof; Details thereof
- H01L31/08—Semiconductor devices sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation; Processes or apparatus specially adapted for the manufacture or treatment thereof or of parts thereof; Details thereof in which radiation controls flow of current through the device, e.g. photoresistors
- H01L31/10—Semiconductor devices sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation; Processes or apparatus specially adapted for the manufacture or treatment thereof or of parts thereof; Details thereof in which radiation controls flow of current through the device, e.g. photoresistors characterised by potential barriers, e.g. phototransistors
- H01L31/115—Devices sensitive to very short wavelength, e.g. X-rays, gamma-rays or corpuscular radiation
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L27/00—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate
- H01L27/14—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate including semiconductor components sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/24—Measuring radiation intensity with semiconductor detectors
- G01T1/244—Auxiliary details, e.g. casings, cooling, damping or insulation against damage by, e.g. heat, pressure or the like
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L27/00—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate
- H01L27/14—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate including semiconductor components sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation
- H01L27/144—Devices controlled by radiation
- H01L27/146—Imager structures
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L27/00—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate
- H01L27/14—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate including semiconductor components sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation
- H01L27/144—Devices controlled by radiation
- H01L27/146—Imager structures
- H01L27/14665—Imagers using a photoconductor layer
- H01L27/14676—X-ray, gamma-ray or corpuscular radiation imagers
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L31/00—Semiconductor devices sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation; Processes or apparatus specially adapted for the manufacture or treatment thereof or of parts thereof; Details thereof
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L31/00—Semiconductor devices sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation; Processes or apparatus specially adapted for the manufacture or treatment thereof or of parts thereof; Details thereof
- H01L31/02—Details
- H01L31/02002—Arrangements for conducting electric current to or from the device in operations
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L31/00—Semiconductor devices sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation; Processes or apparatus specially adapted for the manufacture or treatment thereof or of parts thereof; Details thereof
- H01L31/02—Details
- H01L31/0203—Containers; Encapsulations, e.g. encapsulation of photodiodes
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L27/00—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate
- H01L27/14—Devices consisting of a plurality of semiconductor or other solid-state components formed in or on a common substrate including semiconductor components sensitive to infrared radiation, light, electromagnetic radiation of shorter wavelength or corpuscular radiation and specially adapted either for the conversion of the energy of such radiation into electrical energy or for the control of electrical energy by such radiation
- H01L27/144—Devices controlled by radiation
- H01L27/146—Imager structures
- H01L27/14601—Structural or functional details thereof
- H01L27/14618—Containers
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01L—SEMICONDUCTOR DEVICES NOT COVERED BY CLASS H10
- H01L2924/00—Indexing scheme for arrangements or methods for connecting or disconnecting semiconductor or solid-state bodies as covered by H01L24/00
- H01L2924/0001—Technical content checked by a classifier
- H01L2924/0002—Not covered by any one of groups H01L24/00, H01L24/00 and H01L2224/00
Definitions
- the present invention relates to a radiation detector that includes a radiation-sensitive semiconductor that generates a charge upon incidence of radiation, and is used in the medical field, the industrial field, and the nuclear field.
- a radiation (for example, X-ray) detector indirectly generates a light from the incidence of radiation (for example, an X-ray), and generates a charge from the light power, thereby indirectly from the radiation to the charge.
- a “direct conversion type” detector that detects radiation by converting it, and a direct conversion type detector that detects radiation by converting it directly into a charge from the radiation source by generating charge by the incidence of radiation. There is a detector. Note that a radiation-sensitive semiconductor generates a charge.
- the direct conversion type radiation detector includes an active matrix substrate 51, a radiation-sensitive semiconductor 52 that generates a charge upon incidence of radiation, and a common electrode 53 for applying a bias voltage. It has.
- the active matrix substrate 51 is formed with a plurality of collecting electrodes (not shown) on the radiation incident surface side, and an electric circuit (not shown) for accumulating the charges collected by each collecting electrode (not shown) is arranged. It is configured.
- Each collection electrode is set in a two-dimensional matrix arrangement within the radiation detection effective area SA.
- a semiconductor 52 is laminated on the incident surface side of the collecting electrode of the active matrix substrate 51, and a common electrode 53 is formed in a planar shape on the incident side of the semiconductor 52 and laminated.
- a lead wire 54 for supplying bias voltage is connected to the incident surface of the common electrode 53.
- a bias voltage is applied from a bias supply power source (not shown) to a common electrode 53 for applying a bias voltage via a lead wire 54 for supplying a bias voltage.
- a bias voltage is applied from a bias supply power source (not shown) to a common electrode 53 for applying a bias voltage via a lead wire 54 for supplying a bias voltage.
- the bias voltage applied charges are generated by the radiation-sensitive semiconductor 52 as the radiation enters.
- the generated charge is once collected by the collecting electrode.
- the collected charge is collected as a radiation detection signal for each collection electrode by an electrical circuit for storage and readout that also includes capacitors, switching elements, and electrical wiring. put out.
- Each collection electrode of the two-dimensional matrix array corresponds to an electrode (pixel electrode) corresponding to each pixel of the radiographic image.
- the semiconductor 52 is made of amorphous selenium, CdTe, CdZnTe, Pbl, Hgl, TlBr, etc.
- a large-area, thick-film radiation-sensitive semiconductor 52 can be easily formed by vacuum deposition.
- these amorphous selenium and non-selenium polycrystalline semiconductors are relatively soft and easily damaged.
- FIG. 11 for example, Patent Document 1.
- an insulating base 55 is disposed on the incident surface of the semiconductor 52 outside the radiation detection effective area SA.
- the common electrode 53 is formed so as to cover at least a part of the pedestal 55, and the lead wire 54 is formed so as to be connected to a position on the pedestal 55 on the incident surface of the common electrode 53.
- the pedestal 55 softens the impact applied when the lead wire 54 is connected to the common electrode 53. As a result, it is possible to prevent damage to the radiation-sensitive semiconductor that causes the breakdown voltage failure, and to avoid performance degradation such as a breakdown voltage failure. Further, since the pedestal 55 is disposed outside the radiation detection effective area SA, it is possible to prevent the radiation detection function from being impaired by providing the pedestal.
- an insulating auxiliary plate 56 having a thermal expansion coefficient comparable to that of the active matrix substrate 51 covers the semiconductor 52 and the common electrode 53 from a curable synthetic resin.
- the auxiliary plate 56 is fixedly formed by the resin film 57.
- release Radiation detection effective area SA The resin film 57 is formed to be thicker outside the radiation detection effective area SA including the connection portion of the common electrode 53 to the lead wire 54 than in the SA (see, for example, Patent Documents). 2).
- the stress applied to the semiconductor 52 caused by the resin film 57 can be reduced by forming the resin film 57 thin.
- Radiation detection effective area Outside the SA by forming a thick resin film 57, the degradation of the creeping discharge prevention function of the resin film 57 can be suppressed.
- Patent Document 1 Japanese Patent Laid-Open No. 2005-86059 (Pages 1, 2, 4-12, Fig. 1, 2, 6-9)
- Patent Document 2 Japanese Patent Laid-Open No. 2005-286183 (Page 1-10, Fig. 1)
- the present invention has been made in view of such circumstances, can prevent performance degradation caused by connecting a lead wire to a common electrode, and can prevent thermal deformation stress and radiation attenuation.
- An object of the present invention is to provide a radiation detector that can avoid the problem. Means for solving the problem
- the present invention has the following configuration.
- the radiation detector according to the present invention is a radiation detector that detects radiation, and includes a radiation-sensitive semiconductor that generates a charge upon incidence of radiation, and a bias formed in a planar shape toward the incident side of the semiconductor.
- Common electrode for voltage application and input of the common electrode
- a lead wire for supplying a bias voltage connected to the incident surface, and the location of the semiconductor located at the connection portion of the common electrode to the lead wire is not within the radiation detection effective area.
- the insulating pedestal is disposed so as to fill the portion located at the connecting portion, and the common electrode is formed so as to cover at least a part of the pedestal. Is formed so as to be connected to a position on the pedestal of the incident surface of the common electrode.
- the semiconductor radiation sensitive type located at the connection portion of the common electrode (for bias voltage application) to the lead wire (for bias voltage power supply)
- the part is formed so as to be recessed more concavely than other parts of the semiconductor within the range that does not reach the radiation detection effective area, and an insulating pedestal is disposed so as to fill the part located at the connection part, and the common electrode Is formed so as to cover at least a part of the pedestal described above, and the lead wire is formed so as to be connected to a position located on the pedestal on the incident surface of the common electrode.
- the lead wire is formed so as to be connected to a position located on the pedestal on the incident surface of the common electrode, and the position located in the above-described connection portion (that is, the concave recess portion of the semiconductor) is filled.
- the pedestal softens the impact applied when connecting the lead wire to the common electrode. As a result, it is possible to prevent damage to the radiation-sensitive semiconductor that causes the breakdown voltage failure, and avoid performance degradation such as a breakdown voltage failure.
- the pedestal is disposed so as to fill the portion located in the connection portion, and the common electrode is formed so as to cover at least a part of the pedestal, on the opposite side to the incident side of the common electrode
- the power that the pedestal existed in the connection area In the other area there was a semiconductor that was buried by the pedestal.
- the thickness of the pedestal and common electrode at the connection portion is almost the same as the thickness of the semiconductor and common electrode at other portions, so that problems of thermal deformation stress and radiation attenuation can be avoided. .
- the common electrode In order to prevent creeping discharge, it is preferable to form the common electrode as far as possible inside the semiconductor as long as it does not reach the radiation detection effective area.
- the location in the semiconductor located at the connection portion described above reaches the radiation detection effective area.
- the lead wire must be connected to the entrance surface of the common electrode, and the lead wire should be connected to the pedestal on the entrance surface of the common electrode.
- a pedestal exists on the side opposite to the incident side of the common electrode at least in the connection portion. Therefore, the common electrode is formed outside the semiconductor at least in the connection portion.
- connection portion is formed so as to protrude more than the other portion of the common electrode. Is preferred.
- the connection portion is formed outside the semiconductor at the connection portion.
- the above-described example of the present invention is a one-dimensional shape set in the above-described radiation detection effective area! /
- a two-dimensional matrix array is formed with a plurality of collecting electrodes formed on the entrance surface, and an active matrix substrate configured to include an electric circuit for accumulating and reading out charges collected by each collecting electrode,
- the semiconductor is stacked on the incident surface side of the collecting electrode of the active matrix substrate.
- a bias voltage is applied to a common electrode (for applying a bias voltage) via a lead wire (for supplying a bias voltage).
- a charge is generated in the (radiation-sensitive) semiconductor as radiation enters. This generated charge is once collected by the collecting electrode.
- the collected charge is taken out as a radiation detection signal for each collecting electrode by the electric circuit for accumulation and reading.
- a one-dimensional array type or two-dimensional array type capable of detecting a one-dimensional intensity distribution or a two-dimensional intensity distribution of radiation projected on the radiation detection effective area. It is a radiation detector.
- a radiation detector that is, a radiation detector including an active matrix substrate
- an insulating auxiliary plate having a thermal expansion coefficient comparable to that of the active matrix substrate is common to the semiconductor. It is preferable to fix and form the auxiliary plate with a curable synthetic resin so as to cover the electrode. This fixed formation makes it possible to change the It is possible to prevent dielectric breakdown due to warpage due to change in degree, cracks, and the like.
- "Akuti blanking matrix substrate and the insulating auxiliary plate having a thermal expansion coefficient comparable" is the digit in the thermal expansion coefficient shows comparable, for example, thermal expansion coefficient of 4.
- OX 10- 6 in the case of Z ° C indicates the range of 1. 0 X 10- 6 ⁇ 1. 0 X 10- 5 Z ° c.
- the film thickness of the curable synthetic resin described above is within the radiation detection effective area rather than outside the radiation detection effective area including the connection portion of the common electrode to the lead wire. It is preferable to form the curable synthetic resin so that it is thinner.
- the stress applied to the semiconductor due to the resin film made of the curable synthetic resin can be reduced in the radiation detection effective area, and the radiation detection effective area can be reduced. Outside, the degradation of the creeping discharge preventing function of the resin film can be suppressed.
- the semiconductor is an amorphous semiconductor of high-purity amorphous selenium (a-Se), alkali metal such as Na, halogen such as C1, or selenium and selenium compound doped with As or Te, CdTe, CdZnTe, Pbl, Hgl, TlBr, etc.
- a-Se high-purity amorphous selenium
- alkali metal such as Na
- halogen such as C1
- selenium and selenium compound doped with As or Te CdTe, CdZnTe, Pbl, Hgl, TlBr, etc.
- Amorphous selenium, alkali metals, halogens, selenium doped with As or Te, amorphous semiconductors of selenium compounds, and non-selenium polycrystalline semiconductors are excellent in large area suitability and thick film suitability. On the other hand, they are less susceptible to Mohs hardness and tend to be damaged, but the pedestal can soften the impact applied when connecting the lead wires to the common electrode and prevent damage. Large area and thick film of (radiation sensitive) semiconductor can be easily achieved.
- the pedestal is preferably formed using a hard resin material such as epoxy resin, polyurethane resin, or acrylic resin.
- a hard resin material high hardness after curing
- the pedestal is a soft material such as silicone resin or synthetic rubber. Compared to, it is difficult to expand and contract and has an excellent buffering function, so the pedestal can sufficiently soften the impact applied when connecting the lead wire to the common electrode.
- the thickness of the pedestal is approximately the same as the thickness of the semiconductor. Is preferred.
- the pedestal is disposed so as to fill the portion of the common electrode connected to the lead wire, and the common electrode is formed so as to cover at least a part of the pedestal!
- the thickness of the pedestal and common electrode at the connection part and the force at which the thickness of the semiconductor and common electrode at the other part is approximately the same.To ensure that the thickness of the pedestal is the same as the semiconductor thickness To a degree.
- the thickness of the pedestal is comparable to the thickness of the semiconductor.
- an insulating resin material is used to fill a gap between the recessed portion of the semiconductor and the pedestal.
- the pedestal is disposed so as to fill the portion located in the connection portion, there is a possibility that a gap (step) is formed due to a difference in thickness between the recessed portion of the semiconductor and the pedestal.
- the insulating resin material is one of epoxy resin, polyurethane resin, acrylic resin, silicon resin, and synthetic rubber.
- Another example of the present invention described above is provided with a collimator that avoids hitting an edge and a pedestal including a connection portion to the lead wire of the common electrode when radiation enters the radiation detection effective area. It is. At the edge of the common electrode and the pedestal, the electric field generated by the application of the bias voltage is concentrated, and unexpected radiation may cause a failure of the radiation detector when it hits the radiation. Therefore, by providing a collimator that avoids radiation hitting the edge and pedestal of the common electrode, radiation hits the edge and pedestal of the common electrode where the electric field is concentrated, causing a failure of the radiation detector. An unexpected large current can be prevented from flowing.
- the radiation detector of the present invention in the (radiation sensitive) semiconductor located at the connection portion of the common electrode (for bias voltage application) to the lead wire (for bias voltage power supply)
- the part is formed so as to be recessed more concavely than other parts of the semiconductor within the range that does not reach the radiation detection effective area, and the insulating part is buried so as to fill the part located at the connection part.
- a pedestal is provided, the common electrode is formed so as to cover at least a part of the pedestal described above, and the lead wire is formed so as to be connected to a position on the pedestal on the incident surface of the common electrode! / Therefore, it is possible to avoid performance degradation caused by connecting lead wires to the common electrode, and to avoid problems of thermal deformation stress and radiation attenuation.
- FIG. 1 is a schematic plan view of a direct conversion flat panel X-ray detector (FPD) according to a first embodiment.
- FPD flat panel X-ray detector
- FIG. 2 is a schematic sectional view of a flat panel X-ray detector (FPD) according to Embodiment 1.
- FIG. 3 is a block diagram showing an equivalent circuit of an active matrix substrate of a flat panel X-ray detector (FPD).
- FPD flat panel X-ray detector
- FIG. 4 is a schematic cross-sectional view of an active matrix substrate of a flat panel X-ray detector (FPD).
- FPD flat panel X-ray detector
- FIG. 5 is a schematic sectional view of a flat panel X-ray detector (FPD) protected by an auxiliary plate according to Example 1.
- FPD flat panel X-ray detector
- FIG. 6 (a) is a schematic cross-sectional view including the periphery of the gap, and (b) is a schematic cross-sectional view formed by filling a gap with an insulating resin material.
- FIG. 7] (a) to (c) are schematic cross-sectional views respectively showing combinations of intermediate layers which are carrier-selective high-resistance semiconductor layers.
- FIG. 8 is a schematic sectional view of a flat panel X-ray detector (FPD) according to Embodiment 2.
- FIG. 9 is a schematic sectional view of a flat panel X-ray detector (FPD) according to a modification.
- FIG. 10 is a schematic sectional view of a conventional radiation detector.
- FIG. 11 is a schematic cross-sectional view of a conventional radiation detector different from FIG.
- FIG. 12 is a schematic sectional view of another conventional radiation detector different from those in FIGS. 10 and 11. Explanation of symbols
- a location in the radiation-sensitive semiconductor located at the connection portion of the common electrode for applying the nous voltage to the lead wire for supplying the bias voltage is set to another location in the semiconductor within the range not reaching the radiation detection effective area.
- An insulative pedestal is provided so as to fill the portion located at the connecting portion, and the common electrode is formed so as to cover at least a part of the pedestal described above, and the lead wire is common.
- FIG. 1 is a schematic plan view of a direct conversion flat panel X-ray detector (hereinafter abbreviated as “FPD” where appropriate) according to the first embodiment
- FIG. 2 is a flat panel type according to the first embodiment
- Fig. 3 is a schematic cross-sectional view of an X-ray detector (FPD)
- Fig. 3 is a block diagram showing an equivalent circuit of an active matrix substrate of a flat panel X-ray detector (FPD)
- Fig. 4 is a flat panel X
- FIG. 5 is a schematic cross-sectional view of an active matrix substrate of a line detector (FPD)
- FIG. 1 is a schematic plan view of a direct conversion flat panel X-ray detector (hereinafter abbreviated as “FPD” where appropriate) according to the first embodiment
- FIG. 2 is a flat panel type according to the first embodiment
- Fig. 3 is a schematic cross-sectional view of an X-ray detector (FPD)
- Fig. 3 is a
- Example 5 is a schematic cross-sectional view of a flat panel X-ray detector (FPD) protected by an auxiliary plate according to the first embodiment.
- FPD flat panel X-ray detector
- Example 1 including Example 2 described later, a flat panel X-ray detector (FPD) will be described as an example of a radiation detector.
- the FPD according to the first embodiment is an active matrix substrate 1 and a radiation-sensitive type that generates charges by the incidence of radiation (X-rays in the first and second embodiments).
- the active matrix substrate 1 has a plurality of collecting electrodes 11 formed on the radiation incident surface side, and an electric circuit 12 for accumulating and reading out the charges collected by the collecting electrodes 11 is arranged. It is configured.
- Each collection electrode 11 is set in a two-dimensional matrix arrangement within the radiation detection effective area SA.
- the active matrix substrate 1 corresponds to the active matrix substrate in the present invention
- the radiation-sensitive semiconductor 2 corresponds to the radiation-sensitive semiconductor in the present invention
- the common electrode 3 for applying a bias voltage is the present invention.
- the radiation detection effective area SA corresponds to the radiation detection effective area in the present invention.
- the semiconductor 2 is stacked on the incident surface side of the collecting electrode of the active matrix substrate 1, and the common electrode 3 is formed in a planar shape on the incident side of the semiconductor 2 and stacked. Speak.
- a lead wire 4 for supplying bias voltage is connected to the incident surface of the common electrode 3.
- a lead wire 4 such as a copper wire is connected to the common electrode 3 via a conductive paste (eg, silver paste).
- the lead wire 4 for supplying the noisy voltage corresponds to the lead wire for supplying the bias voltage in the present invention.
- the active matrix substrate 1 is formed with the collecting electrode 11 as described above, and the storage / reading electric circuit 12 is provided.
- the electrical circuit for storage and readout 1 2 is composed of a capacitor 12A and TFT (thin film field effect transistor) 1 2B as a switching element, gate line 12a, data line 12b, etc., and one capacitor 12A for each collecting electrode 11 And one TFT12B is associated and connected.
- the collecting electrode 11 corresponds to the collecting electrode in the present invention
- the storage / reading electric circuit 12 corresponds to the storing / reading electric circuit in the present invention.
- a gate driver 13, a charge-voltage conversion type amplifier 14, a multiplexer 15, and an AZD conversion 16 are arranged and connected around the electrical circuit 12 for storing and reading out of the active matrix substrate 1. .
- the gate driver 13, the charge / voltage conversion amplifier 14, the multiplexer 15, and the AZD conversion 16 are connected to a substrate different from the active matrix substrate 1. Part or all of the gate driver 13, the charge / voltage conversion amplifier 14, the multiplexer 15, and the A / D converter 16 may be incorporated in the active matrix substrate 1.
- a bias voltage is supplied from a bias supply power source (not shown) via a bias voltage supply lead wire 4 and a common electrode 3 for bias voltage application. Apply.
- the charges collected by the collecting electrode 11 are accumulated in the capacitor 12A.
- a read signal is sequentially applied from the gate driver 13 to the gate of each TFT 12B through the gate line 12a.
- TFT12 B to which the read signal is applied shifts from OFF to ON.
- the data line 12b connected to the source of the transferred TFT 12B is sequentially switched and connected by the multiplexer 15, the charge accumulated in the capacitor 12A is read out from the TFT 12B via the data line 12b.
- the read charge is amplified by the charge-voltage conversion amplifier 14 and sent to the AZD converter 16 as a radiation detection signal (X-ray detection signal in Examples 1 and 2) for each collection electrode 11 by the multiplexer 15 and analog. The value is converted to a digital value.
- an FPD when an FPD is provided in an X-ray fluoroscopic apparatus, an X-ray detection signal is sent to an image processing circuit at a subsequent stage, image processing is performed, and a two-dimensional X-ray fluoroscopic image or the like is output.
- Each collection electrode 11 in the two-dimensional matrix array corresponds to an electrode (pixel electrode) corresponding to each pixel of the radiation image (here, a two-dimensional fluoroscopic image).
- the radiation detection signal X-ray detection signal in Examples 1 and 2
- a radiation image corresponding to the two-dimensional intensity distribution of the radiation projected onto the radiation detection effective area SA here, a two-dimensional fluoroscopic image
- the FPD according to the first embodiment including the second embodiment described later can detect the two-dimensional intensity distribution of the radiation (X-rays in the first and second embodiments) projected onto the radiation detection effective area SA. It is a two-dimensional array type radiation detector.
- the location in the semiconductor 2 located at the connection portion of the common electrode 3 to the lead wire 4 is within the range that does not reach the radiation detection effective area SA. Also recessed in a concave shape Form.
- An insulating base 5 is disposed so as to fill the location where the connecting portion is located.
- the common electrode 3 is formed so as to cover a part of the pedestal 5, and the lead wire 4 is formed so as to be connected to a position on the pedestal 5 on the incident surface of the common electrode 3.
- the insulating base 5 corresponds to the insulating base in the present invention.
- the lead wire 4 is formed so as to be connected to a position located on the pedestal 5 on the incident surface of the common electrode 3, and the position located at the above-described connection portion (that is, the concave recess portion of the semiconductor 2)
- the pedestal 5 can soften the impact applied when the lead wire 4 is connected to the common electrode 3.
- it is possible to prevent damage to the radiation-sensitive semiconductor 2 that causes a breakdown voltage failure, and to avoid performance degradation such as a breakdown voltage failure.
- the base 5 is disposed so as to fill the portion located in the connection portion, and the common electrode 3 is formed so as to cover a part of the base 5, the incident side of the common electrode 3 is defined as On the other side, the power of the pedestal 5 existing at the connection part is the semiconductor 2 embedded in the pedestal 5 at the other part.
- the thickness of pedestal 5 and common electrode 3 at the connection part is almost the same as the thickness of semiconductor 2 and common electrode 3 at other parts, avoiding problems of thermal deformation stress and radiation attenuation. can do.
- the force common electrode 3 formed so as to cover a part of the pedestal 5 may be formed so that the common electrode 3 covers the entire pedestal 5. Therefore, the common electrode 3 may be formed so as to cover at least a part of the base 5.
- the common electrode 3 can be used in a range not reaching the radiation detection effective area SA. Is formed inside the semiconductor 2.
- the lead In order for the wire 4 to be connected to the common electrode 3 and for the lead wire to be connected to a position on the pedestal 5 of the incident surface of the common electrode 3, as shown in FIG. There is a pedestal 5 on the side opposite to the incident side. Therefore, the common electrode 3 is more than the semiconductor 2 at least in the connection portion.
- connection portion is more convex than the other portions of the common electrode 3. Overhang to form.
- the FPD is protected by the insulating auxiliary plate 6 as shown in FIG.
- an insulating auxiliary plate 6 having a thermal expansion coefficient comparable to that of the active matrix substrate 1 is connected to the semiconductor 2 and the common electrode 3. It is preferable that the auxiliary plate 6 is fixedly formed by a resin film 7 made of a curable synthetic resin so as to cover it.
- the active matrix substrate 1 for example, a glass substrate is used, and as the insulating auxiliary plate 6, for example, a Pyrex (registered trademark) glass substrate or a quartz glass substrate is used.
- the thickness of the glass substrate of the active matrix substrate 1 and the glass substrate of the auxiliary plate 6 is, for example, about 0.5 mm to 1.5 mm.
- an insulating auxiliary plate having the same thermal expansion coefficient as the active matrix substrate means that the digits of the thermal expansion coefficient are the same, for example, the thermal expansion coefficient is 4.
- OX 10— in the case of 6 Z ° C indicates the range of 1. 0 X 10- 6 ⁇ 1. 0 X 10- 5 / ° C.
- the insulating auxiliary plate 6 corresponds to the insulating auxiliary plate in the present invention.
- the film thickness of the above-described resin film 7 is such that the radiation detection effective area SA including the connection portion of the common electrode 3 to the lead wire 4 as shown in FIG. It is preferable to form the resin film 7 so that the radiation detection effective area SA is thinner than the outside.
- a frame frame-shaped spacer 8 formed of ABS grease or the like is erected around the active matrix substrate 1 and the auxiliary plate 6 is supported on the incident side of the spacer 8. .
- the room temperature curable resin composition after curing becomes a resin film 7,
- Auxiliary plate 6 is fixedly formed by a resin film 7 made of curable synthetic resin.
- the auxiliary plate 6 is also divided into pieces 6a and 6b according to each region by dividing the region including the radiation detection effective area SA excluding the outer region and the region of the outer region. As shown in FIG. 5, the auxiliary plate 6 is a thin film piece 6a in the region including the radiation detection effective area SA, and a thick film piece 6b in the outer region, and is thicker between the pieces 6a and 6b. Provide a gear in the vertical direction.
- the auxiliary plate 6 when the auxiliary plate 6 is supported on the spacer 8 and a liquid room temperature curable resin composition is injected and cured between the active matrix substrate 1 and the auxiliary plate 6, the thin film piece 6a and There is a gap in the film thickness of the resin film 7 between the thick film piece 6b. As a result, the resin film 7 is formed so that the inside of the radiation detection effective area SA is thinner than the outside of the radiation detection effective area SA including the connection portion described above.
- the auxiliary plate 6 may be formed by separating the pieces 6a and 6b, or the auxiliary plate 6 may be formed by integrating the pieces 6a and 6b.
- the stress applied to the semiconductor 2 caused by the resin film 7 can be reduced by forming the resin film 7 thinly. Outside the radiation detection effective area SA, it is possible to suppress the degradation of the creeping discharge prevention function of the resin film 7 by forming the resin film 7 thick.
- the thickness of the rosin film 7 in the radiation detection effective area SA is TA and the thickness of the rosin film 7 outside the radiation detection effective area SA is ta, 0.5ta It is preferable to set the film thickness of the resin film 7 so as to satisfy ⁇ TA ⁇ 0.Ita.
- the thickness TA of the resin film 7 is usually in the range of 0.1 mm to 0.5 mm, and the thickness ta of the resin film 7 is usually in the range of 1 mm to 2 mm.
- the thickness of the semiconductor 2 is usually a thick film of about 0.5 mm to l. 5 mm, and the area is, for example, about 20 cm to 50 cm in length and about 20 cm to 50 cm in width. Further, the thickness force of the pedestal 5 is preferably about the same as the thickness of the semiconductor 2. As described above, the pedestal 5 is disposed so as to fill the portion of the common electrode 3 connected to the lead wire 4, and the common electrode 3 is formed so as to cover at least a part of the pedestal 5. The thickness of the base 5 and the common electrode 3 at the connecting portion and the thickness of the semiconductor 2 and the common electrode 3 at the other portions are almost the same. Same as the thickness of semiconductor 2.
- thickness force of pedestal 5 is about the same as the thickness of semiconductor 2” means that the thickness of semiconductor 2 (1 ⁇ 0 5) The thickness is the thickness of the pedestal 5, more preferably, (1 ⁇ 0.2) times to 1 times the thickness of the semiconductor 2 is the range of the thickness of the pedestal 5.
- the pedestal 5 When the pedestal 5 is disposed so as to fill the portion located in the connection portion, as shown in FIG. 6 (a), the thickness of the recessed portion in the semiconductor 2 and the thickness of the pedestal 5 is adjusted. There is a possibility that a gap (step) G is formed due to the difference. In such a case, as shown in FIG. 6 (b), the gap G is formed by filling the gap G using an insulating resin material, so that the continuity between the recessed portion of the semiconductor 2 and the base 5 is increased. It is possible to achieve FPD with excellent stability.
- the insulating resin material may be epoxy resin, polyurethane resin, acrylic resin, silicon resin, or synthetic rubber. Used.
- the radiation-sensitive semiconductor 2 includes amorphous metals such as high-purity amorphous selenium (a-Se) and Na, halogens such as C1, halogens such as C1, and selenium and selenium compounds doped with As and Te, CdTe, CdZnTe , Pbl, Hgl, TlBr, etc.
- amorphous metals such as high-purity amorphous selenium (a-Se) and Na
- halogens such as C1
- C1 halogens
- selenium and selenium compounds doped with As and Te
- CdTe, CdZnTe , Pbl, Hgl, TlBr etc.
- Amorphous selenium, selenium doped with alkali metal or halogen, As or Te, amorphous semiconductors of selenium compounds, and non-selenium-based polycrystalline semiconductors have excellent suitability for large area and thick film. On the other hand, they have a Mohs hardness of 4 or less and are easily damaged. However, the impact applied when the lead wire 4 is connected to the common electrode 3 is softened to prevent the base 5 from being damaged. As a result, the large area and thickness of the semiconductor 2 can be easily achieved. In particular, when a-Se having a specific resistance of 10 9 ⁇ or more, preferably 10 U Q or more, is used for the semiconductor 2, the large area suitability and the film thickness suitability are remarkably excellent!
- the semiconductor 2 is formed on the incident surface (upper surface in FIG. 2), the surface opposite to the incident side (lower surface in FIG. 2), or both surfaces. It also includes a combination with an intermediate layer, which is a carrier-selective high-resistance semiconductor layer.
- an intermediate layer 2a is formed between the semiconductor 2 and the common electrode 3
- an intermediate layer 2b is formed between the semiconductor 2 and the collecting electrode 11 (see FIG. 4).
- the intermediate layer 2a may be formed only between the semiconductor 2 and the common electrode 3, or as shown in FIG.
- the intermediate layer 2b may be formed only between 2 and the collecting electrode 11 (see FIG. 4).
- the dark current can be reduced by providing the carrier selective intermediate layers 2a and 2b.
- the carrier selectivity here refers to the property that the contribution rate to the charge transfer action differs significantly between electrons and holes, which are charge transfer media (carriers) in a semiconductor.
- the following modes may be mentioned.
- a positive bias voltage is applied to the common electrode 3
- a material having a large contribution ratio of electrons is used for the intermediate layer 2a.
- the injection of holes from the common electrode 3 is blocked, and the dark current can be reduced.
- the intermediate layer 2b a material having a large contribution ratio of holes is used. Thereby, the injection of electrons from the collecting electrode 11 is blocked, and the dark current can be reduced.
- the thickness of the carrier-selective intermediate layers 2a and 2b is usually preferably in the range of 0.1 m to 10 ⁇ m. If the thickness of the intermediate layer 2a, 2b is less than 0 .: Lm, there is a tendency that dark current cannot be sufficiently suppressed. Conversely, if the thickness exceeds 10 m, radiation detection tends to be hindered (for example, the sensitivity decreases). Tend to appear).
- Semiconductors used for the carrier-selective intermediate layers 2a and 2b include Sb S and ZnTe.
- Selenium doped with gen or As or Te and amorphous semiconductors of selenium compounds are examples of those that have excellent suitability for large areas. These semiconductors are thin and easily damaged, but the base 5 can soften the impact applied when connecting the lead wire 4 to the common electrode 3 and prevent damage.
- the carrier-selective intermediate layers 2a and 2b are excellent in large area suitability.
- those having a large contribution of electrons include polycrystalline semiconductors such as CeO, CdS, CdSe, ZnSe, and ZnS, which are n-type semiconductors, and alkali gold.
- Amorphous such as amorphous Se doped with As or Te to reduce the contribution of holes A case is mentioned.
- a polycrystalline semiconductor such as a p-type semiconductor such as ZnTe, or an amorphous Se or the like that is doped with halogen to reduce the contribution of electrons.
- the body is mentioned.
- the insulating base 5 using a hard resin material such as epoxy resin, polyurethane resin, acrylic resin, or the like.
- a hard resin material high hardness after curing
- the base 5 is soft like silicone resin synthetic rubber. Since it is difficult to expand and contract compared to the material and has a superior buffering function, the pedestal 5 can sufficiently moderate the impact applied when the lead wire 4 is connected to the common electrode 3.
- FIG. 8 is a schematic cross-sectional view of a flat panel X-ray detector (FPD) according to the second embodiment.
- the parts common to the above-described first embodiment are denoted by the same reference numerals, description thereof is omitted, and illustration is omitted.
- the FPD according to the second embodiment includes a connection portion of the common electrode 3 to the lead wire 4 when radiation (here, X-rays) enters the radiation detection effective area SA. It has a collimator 9 to avoid hitting the edge and pedestal 5.
- the collimator 9 corresponds to the collimator in the present invention.
- the second embodiment is provided with a collimator 9 that prevents the radiation from hitting the edge of the common electrode 3 and the pedestal 5.
- the radiation does not strike the edge of the common electrode 3 and the pedestal 5, and the radiation is detected.
- the opening 9A of the collimator 9 is provided so as to enter the effective area SA.
- the semiconductor 2 is formed on the incident surface, the surface opposite to the incident side, or both in addition to the sensitive semiconductor 2 described above. It also includes a combination with an intermediate layer which is a carrier-selective high-resistance semiconductor layer.
- the radiation detector represented by the flat panel X-ray detector is a two-dimensional array type.
- the radiation detector of the present invention has a collecting electrode 1
- a one-dimensional array type formed with a dimensional matrix arrangement may be used, or a non-array type having only one electrode for extracting radiation detection signals may be used.
- the X-ray detector is taken as an example of the radiation detector.
- the radiation detector (for example, gamma ray detector) that detects radiation other than the force X-ray (for example, gamma ray) It can also be applied to.
- Embodiment 1 and Embodiment 2 may be combined with each other. That is, as in Example 1, a resin film made of a curable synthetic resin so that an insulating auxiliary plate 6 having a thermal expansion coefficient comparable to that of the active matrix substrate 1 covers the semiconductor 2 and the common electrode 3. 7 includes a structure in which the auxiliary plate 6 is fixedly formed (see FIG. 5) and, as in the second embodiment, when the radiation enters the radiation detection effective area SA, the connection portion of the common electrode 3 to the lead wire 4 is included. Can be combined with a structure with a collimator 9 (see Fig. 8) to avoid hitting the edges and pedestal 5! / ,.
- the common electrode 3 is formed on the inner side of the semiconductor 2 within the range not reaching the radiation detection effective area SA in order to prevent the creeping discharge. If not, the edge of the common electrode 3 and the edge of the semiconductor 2 may be aligned, or the common electrode 3 may be formed outside the semiconductor 2. Thus, when the common electrode 3 is not formed inside the semiconductor 2, the connection portion of the common electrode 3 to the lead wire 4 is not necessarily shared. It is not necessary to form the projection electrode 3 so that it protrudes more than other portions. Of course, even when the common electrode 3 is not formed on the inner side of the semiconductor 2, the above-described connection portion may be formed so as to protrude from other portions of the common electrode 3.
- the epoxy resin, polyurethane resin, acrylic resin used as the material of the pedestal 5 is disposed in the recessed portion of the semiconductor 2.
- the base 5 may be formed by filling and curing a hard resin material such as resin, or it may be formed by mounting the base 5 previously molded into a solid shape in the recess.
- Example 1 the film thickness of the resin film 7 made of a curable synthetic resin is larger than that outside the radiation detection effective area SA including the connection portion of the common electrode 3 to the lead wire 4. Radiation detection effective area SA was formed so that the inner side of SA was thinner (see Fig. 5). However, as shown in Fig. 9, the thickness of the resin membrane 7 was uniform throughout. As shown, form the rosin film 7.
- Example 1 a curable synthetic resin is used so that the insulating auxiliary plate 6 having the same thermal expansion coefficient as that of the active matrix substrate 1 covers the semiconductor 2 and the common electrode 3.
- a liquid room temperature curable resin composition is injected and cured between the active matrix substrate 1 and the auxiliary plate 6, but the common electrode 3 and The auxiliary plate 6 may be supported after the room temperature curable resin composition is applied to the incident surface of the lead wire 4.
- the spacer 8 as shown in FIG. 5 can be made thinner than necessary.
- the present invention is suitable for a direct conversion type radiation detector.
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Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
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CN2006800533796A CN101390213B (zh) | 2006-02-23 | 2006-02-23 | 放射线检测器 |
KR1020087021084A KR101064856B1 (ko) | 2006-02-23 | 2006-02-23 | 방사선 검출기 |
JP2008501525A JPWO2007096967A1 (ja) | 2006-02-23 | 2006-02-23 | 放射線検出器 |
PCT/JP2006/303275 WO2007096967A1 (ja) | 2006-02-23 | 2006-02-23 | 放射線検出器 |
US12/280,306 US7875856B2 (en) | 2006-02-23 | 2006-02-23 | Radiation detector |
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PCT/JP2006/303275 WO2007096967A1 (ja) | 2006-02-23 | 2006-02-23 | 放射線検出器 |
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WO2007096967A1 true WO2007096967A1 (ja) | 2007-08-30 |
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PCT/JP2006/303275 WO2007096967A1 (ja) | 2006-02-23 | 2006-02-23 | 放射線検出器 |
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US (1) | US7875856B2 (ja) |
JP (1) | JPWO2007096967A1 (ja) |
KR (1) | KR101064856B1 (ja) |
CN (1) | CN101390213B (ja) |
WO (1) | WO2007096967A1 (ja) |
Cited By (6)
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JP2009088183A (ja) * | 2007-09-28 | 2009-04-23 | Fujifilm Corp | 放射線検出器 |
JP2009099941A (ja) * | 2007-09-28 | 2009-05-07 | Fujifilm Corp | 放射線検出器、放射線検出器の製造方法、塗布液及び有機高分子層の製造方法 |
WO2009056967A3 (en) * | 2007-11-01 | 2010-03-18 | Oy Ajat, Ltd. | Cdtd/cdznte radiation imaging detector and high/biasing voltage means |
EP2053658A3 (en) * | 2007-10-23 | 2012-05-09 | FUJIFILM Corporation | Image detector |
JP5104857B2 (ja) * | 2007-05-21 | 2012-12-19 | 株式会社島津製作所 | 放射線検出器 |
KR101318455B1 (ko) * | 2008-09-10 | 2013-10-16 | 가부시키가이샤 시마즈세이사쿠쇼 | 방사선 검출기 |
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US8563940B2 (en) | 2009-04-03 | 2013-10-22 | Shimadzu Corporation | Radiation detector manufacturing method, a radiation detector, and a radiographic apparatus |
WO2010125608A1 (ja) * | 2009-04-30 | 2010-11-04 | 株式会社島津製作所 | 放射線検出器 |
CN103081127B (zh) * | 2010-07-06 | 2016-03-30 | 株式会社岛津制作所 | 放射线检测器的制造方法 |
CN103534808B (zh) * | 2011-05-30 | 2016-02-10 | 株式会社岛津制作所 | 放射线检测器 |
JP6502731B2 (ja) | 2015-04-13 | 2019-04-17 | キヤノン株式会社 | 放射線撮像装置及び放射線撮像システム |
JP6535271B2 (ja) * | 2015-11-09 | 2019-06-26 | 浜松ホトニクス株式会社 | 放射線検出器、及び放射線検出器の製造方法 |
CN105510952B (zh) * | 2015-12-24 | 2019-09-13 | 同方威视技术股份有限公司 | 飞行模式CdZnTe巡检系统和巡检方法 |
KR102630173B1 (ko) | 2017-12-27 | 2024-01-26 | 엘지디스플레이 주식회사 | 엑스레이검출장치 |
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JP5104857B2 (ja) * | 2007-05-21 | 2012-12-19 | 株式会社島津製作所 | 放射線検出器 |
JP2009088183A (ja) * | 2007-09-28 | 2009-04-23 | Fujifilm Corp | 放射線検出器 |
JP2009099941A (ja) * | 2007-09-28 | 2009-05-07 | Fujifilm Corp | 放射線検出器、放射線検出器の製造方法、塗布液及び有機高分子層の製造方法 |
EP2053658A3 (en) * | 2007-10-23 | 2012-05-09 | FUJIFILM Corporation | Image detector |
WO2009056967A3 (en) * | 2007-11-01 | 2010-03-18 | Oy Ajat, Ltd. | Cdtd/cdznte radiation imaging detector and high/biasing voltage means |
US7741610B2 (en) | 2007-11-01 | 2010-06-22 | Oy Ajat Ltd. | CdTe/CdZnTe radiation imaging detector and high/biasing voltage means |
JP2011501149A (ja) * | 2007-11-01 | 2011-01-06 | オイ アジャト, リミテッド | CdTe/CdZnTe放射線イメージング検出器及び高/バイアス電圧手段 |
KR101318455B1 (ko) * | 2008-09-10 | 2013-10-16 | 가부시키가이샤 시마즈세이사쿠쇼 | 방사선 검출기 |
US8564082B2 (en) | 2008-09-10 | 2013-10-22 | Shimadzu Corporation | Radiation detector |
Also Published As
Publication number | Publication date |
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CN101390213A (zh) | 2009-03-18 |
CN101390213B (zh) | 2010-06-16 |
US20090050813A1 (en) | 2009-02-26 |
KR20080094804A (ko) | 2008-10-24 |
US7875856B2 (en) | 2011-01-25 |
JPWO2007096967A1 (ja) | 2009-07-09 |
KR101064856B1 (ko) | 2011-09-14 |
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