KR20150100243A - Digital radiation detector - Google Patents

Digital radiation detector Download PDF

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KR20150100243A
KR20150100243A KR1020140021799A KR20140021799A KR20150100243A KR 20150100243 A KR20150100243 A KR 20150100243A KR 1020140021799 A KR1020140021799 A KR 1020140021799A KR 20140021799 A KR20140021799 A KR 20140021799A KR 20150100243 A KR20150100243 A KR 20150100243A
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South Korea
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radiation
sensing
layer
pattern
medium layer
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KR1020140021799A
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Korean (ko)
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KR101684730B1 (en
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김정민
김기현
윤용수
김현지
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고려대학교 산학협력단
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Priority to KR1020140021799A priority Critical patent/KR101684730B1/en
Priority to PCT/KR2015/001771 priority patent/WO2015130063A1/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4283—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by a detector unit being housed in a cassette
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
    • G—PHYSICS
    • G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
    • G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
    • G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
    • G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
    • G21K1/025—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using multiple collimators, e.g. Bucky screens; other devices for eliminating undesired or dispersed radiation

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
  • Mathematical Physics (AREA)
  • Radiology & Medical Imaging (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of Radiation (AREA)

Abstract

The present invention relates to a digital radiation detector, which comprises: a radiation medium layer responding to radiation; a sensing substrate layer coupled to a surface of one side of the radiation medium layer, and having a plurality of sensing pixels to sense a response of the radiation medium layer; a support layer coupled to the surface of the other side of the radiation medium layer to protect the radiation medium layer; and a scattered ray removal pattern formed on the support layer to shield a scattered ray. In addition, a surface of the sensing substrate layer, which faces the radiation medium layer, is divided into an effective response area, which includes at least one area of each of the sensing pixels to sense the response of the radiation medium layer, and a non-response area corresponding to the part other than the effective response area. Also, the scattered ray removal pattern is formed in a pattern corresponding to the non-response area. Therefore, the present invention ensures to remove a scattered ray even without installing a scattered ray removal lattice to remove the scattered ray, and can reduce both the size of a radioactive examination apparatus and the surface dose of a patient.

Description

[0001] DIGITAL RADIATION DETECTOR [0002]

The present invention relates to a digital radiation detector, and more particularly, to a digital radiation detector capable of removing a scattered ray without providing a scattering line removing grid for removing a scattering line, reducing the size of a radiation examination apparatus, To a digital radiation detector.

The conversion of radiation including X-rays into a signal that can be perceived by humans, that is, an electrical signal is called radiation detection. A sensor for detecting the radiation, that is, a sensor for detecting radiation, is called a radiation detector detector, and a device for capturing an image of a human body by applying a radiation detector is called a radiation detection device.

Conventionally, a conventional radiographic apparatus has been applied to an analog system in which a film is directly printed. In recent years, a digital radiographic detector (30, see FIG. 1) Devices are widely used.

BRIEF DESCRIPTION OF DRAWINGS FIG. 1 is a diagram showing an example of a configuration of a digital radiography inspection apparatus. FIG. 1, the digital radiography system includes a radiation irradiation unit 10 for irradiating a patient with a radiation, a digital radiation detector 10 for detecting radiation transmitted by the radiation irradiation unit 10, (30), and an image processing device (40) such as a computer for image formation based on the radiation detected by the digital radiation detector (30). Between the patient and the digital radiation detector 30, a grating for removing the scattering line 3 in the radiation is disposed.

FIG. 2 is a diagram showing the structure of a conventional digital radiation detector 30. FIG. FIG. 2 (a) is a cross-sectional view of the digital radiation detector 30, and FIG. 2 (b) is a view showing a sensing substrate of the digital room event detector.

2, a conventional digital radiation detector 30 includes a radiation medium layer 32, a sensing substrate layer 31, and a support layer 33. The radiation medium layer 32 is made of radiation-sensitive material. The sensing substrate layer 31 is bonded to one side surface of the radiation medium layer 32 to sense the radiation medium layer 32.

The sensing substrate layer 31 is composed of a plurality of sensing pixels and the sensing pixels are electrically connected to the data lines DL and the voltage lines VL, And senses the response of the radiation medium layer 32 to generate an electric signal. Here, the sensing substrate layer 31 is generally provided in the form of a TFT (Thin Film Transistor) substrate. A support layer 33 is provided on top of the radiation medium layer 32 to protect the radiation medium layer 32.

3 is a view showing the shape of a line of sight which appears when the radiation irradiated from the irradiation unit 10 is irradiated onto the patient's body. 3, the radiation irradiated by the radiation applying unit 10 is transmitted through the transmission line 1 which penetrates the patient's body, the absorption line 2 absorbed by the patient's body, Scattering line (3).

Here, the transmission line 1 and the scattering line 3 contribute to the image formation acquired by the digital radiation detection unit. The transmission line 1 is detected by the digital radiation detection unit to form a dark part of the image, (2) forms a bright portion of the image. That is, a sensing pixel for sensing the transmission line 1 of each of the sensing pixels of the digital radiation detecting unit forms a dark image, and a sensing pixel for not sensing the transmission line 1 is bright Thereby forming an image.

However, in the case of the scattering line (3), the scattering line (3) has a characteristic of being scattered on a slope or a side without directionality, and when it is detected by the digital radiation detector, it forms noise of the image and acts as a cause of lowering the contrast ratio of the image. In order to remove such a scattering line 3, the scattering line removing grating 20 is disposed between the digital radiation detectors 30 of the patient as described above.

FIG. 4 is a view showing a structure of a conventional scattering line removing grating 20. FIG. As shown in FIG. 4, the conventional scattering line removing grating 20 is formed of a material for transmitting radiation, for example, an intermediate material 22 such as aluminum (Al) or carbon fiber And the grid pattern 21 is formed of a material such as lead Pb having a high absorption efficiency of radiation so that the transmission line 1 transmits the intermediate material 22 and the scattering line 3 penetrates the grid pattern 21, So that the scattering line 3 is removed.

In the case of the grid pattern 21 of the grid 20 for removing a scattered ray as described above, since the transmission line 1 transmitted through the patient is also shielded in the corresponding region, the grid 20 for removing the scattered rays is not used It is necessary to increase the exposure multiple of the radiation according to the grating ratio which is the ratio of the pitch of the grating pattern 21 and the thickness of the grating pattern 21. As a result, There is a problem in that the surface dose of the surface is increased.

In addition, due to the use of the scattering line removing grating 20, the pattern of the scattering line removing grating 20 also appears on the image. In order to eliminate such a phenomenon, a digital ray inspection apparatus is provided with a structure for reciprocating the scattering line removing grating 20 in the direction of the plate surface, for example, a motor. In addition to this, There is a problem of growing.

1, since the scattering line eliminating grating 20 is provided between the patient and the digital radiation detector 30, the digital radiation detector 30 is moved farther away from the radiation irradiating section 10 As a result, the radiation dose to be irradiated for improving the sharpness is increased, which results in an increase in the surface dose of the patient.

Accordingly, the grid-integrated digital X-ray detector disclosed in Korean Patent No. 10-0687654 proposes a pattern in which a grid (grid) and a digital X-ray detector are separated by a predetermined distance and a moire pattern generated by a grid is removed However, the above-described problems caused by the use of the scattering line removing grating 20 are retained.

Accordingly, it is an object of the present invention to solve the above-mentioned problems, and it is an object of the present invention to provide an apparatus and a method for removing a scattering line without installing a scattering line removing grid for removing a scattering line, The present invention also provides a digital radiation detector.

The object is achieved in accordance with the present invention by providing a sensing substrate layer having a radiation sensitive medium sensitive to radiation, a sensing substrate layer coupled to one side surface of the radiation sensitive medium layer and having a plurality of sensing pixels for sensing the sensitivity of the radiation sensitive medium layer, A support layer coupled to the other surface of the layer to protect the radiation medium layer; and a scatter line removal pattern formed on the support layer to shield the scattering line; Wherein the surface of the sensing substrate layer facing the radiation medium layer includes at least one area of each sensing pixel, and includes an effective sensing area for sensing a response of the radiation sensing layer, and a non-sensing area other than the effective sensing area ; And the scattering line elimination pattern is formed in a pattern corresponding to the no-excitation region.

Here, a removal groove corresponding to the scattering line removal pattern is formed on a surface of the support layer opposite to the radiation medium layer; The scattering line removal pattern may be formed by filling the removal groove with a radiation shielding material.

The non-responsive region may include a data line spaced apart in a first direction so as to be connected to the plurality of sensing pixels, and a plurality of sensing lines spaced apart from each other in a first direction intersecting the first direction, A voltage line; The scattering line removal pattern may be formed in a pattern corresponding to at least one of the plurality of data lines and the plurality of voltage lines.

The support layer may be formed of graphite or aluminum. The shielding material may include a lead material.

The depth of the removal groove may be determined based on the size of the sensing pixel and the predetermined grid ratio.

And wherein the radiation-sensitive layer comprises a photoconductor responsive to radiation to generate a charge signal; Each of the sense pixels of the sensing substrate layer may sense the charge signal.

Further, the radiation medium layer may include a scintillator responsive to radiation to generate light; Each of the sensing pixels of the sensing substrate layer may sense light from the scintillator.

The removal grooves adjacent to each other may be formed parallel to each other in the vertical direction.

According to the present invention, it is possible to eliminate scattering lines without providing a scattering line removing grid for removing scattering lines, reduce the size of a radiation examination apparatus, and reduce the surface dose of a patient A digital radiation detector is provided.

1 is a view showing an example of a configuration of a digital radiography inspection apparatus,
2 is a view showing a structure of a conventional digital radiation detector,
FIG. 3 is a view showing the shape of a line of sight seen when the radiation irradiated from the irradiation unit is irradiated to the patient's body, and FIG.
FIG. 4 is a view showing a structure of a conventional grating line removing grid,
5 is an exploded perspective view of a digital radiation detector according to the present invention,
6 is a cross-sectional view of a digital radiation detector according to the present invention,
7 and 8 are views for explaining the effect of the digital radiation detector according to the present invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. In describing the digital radiation detector 30 according to the present invention, another configuration of the digital radiation examination apparatus will be described with reference to Fig.

FIG. 5 is an exploded perspective view of a digital radiation detector 30 according to the present invention, and FIG. 6 is a sectional view of a digital radiation detector 300 according to the present invention. 5 and 6, a digital radiation detector 300 according to the present invention includes a sensing substrate layer 310, a radiation medium layer 320, a support layer 330, and a scatter line removal pattern 340 do.

The radiation medium layer 320 is irradiated from the irradiation part 10 and is sensitive to the radiation transmitted through the patient. The sensing substrate layer 310 is composed of a plurality of sensing pixels coupled to one surface of the radiation medium layer 320 to sense the response of the radiation medium layer 320.

In the present invention, the radiation medium layer 320 includes a photoconductor that is responsive to radiation to generate a charge signal, and each of the sensing pixels of the sensing substrate layer 310 is coupled to the radiation medium layer 320 It is assumed that it is arranged to detect the charge signal.

More specifically, ionization during the interaction between the radiation medium layer 320, such as X-rays and the radiation medium layer, such as a photoconductor, Electrone-ion pairs or electron-hole pairs, or charge signals, are generated to induce such electrical signals. Each of the sensing pixels senses the electrical signal, .

In another example, the radiation medium layer 320 may include a scintillator that is responsive to radiation to generate light, and each sensing pixel of the sensing substrate layer 310 may sense light from the scintillator .

The sensing substrate layer 310, as described above, has a plurality of sensing pixels arranged in a matrix to sense the response of the radiation medium layer 320. Here, the surface of the sensing substrate layer 310 facing the radiation medium layer 320 is divided into an effective sensing area VSA and a no sensing area NSA.

The effective response area (VSA) includes at least one region of each of the detection pixels (Pixels), and senses the response of the radiation medium layer (320). That is, the effective response area VSA constitutes a pixel for an actual image shape.

The non-sensitive area corresponds to an area other than the effective sensitive area (VSA), which does not sense the radiation of the radiation medium layer (320). Referring to FIGS. 5 and 6, the sensing substrate layer 310 may include a plurality of data lines DL and a plurality of voltage lines VL electrically connected to a plurality of sensing pixels .

As shown in FIG. 5, the data lines DL are formed spaced apart in the first direction, and the voltage lines VL are formed in the second direction that intersects the first direction. Here, the plurality of data lines DL and the plurality of voltage lines VL correspond to non-sensitive regions.

The support layer 330 is bonded to the other surface of the radiation medium layer 320 to protect and support the radiation medium layer 320. In the present invention, it is exemplified that the support layer 330 is made of a graphite material or an aluminum (Al) material.

The scattering line removing pattern 340 is formed on the supporting layer 330 to absorb the scattering line 3 to shield the scattering line 3. [ The scattering line removal pattern 340 is provided in a pattern corresponding to the non-sensitive region NSA of the sensing substrate layer 310. The plurality of data lines DL and the plurality of And the voltage line VL of FIG.

5, a plurality of data lines DL and a plurality of voltage lines VL are arranged in a pattern corresponding to a plurality of data lines DL and a plurality of voltage lines VL, It should be understood that the present invention may be embodied in many other specific forms without departing from the spirit or scope of the invention.

6, a scattering line removal pattern 340 according to the present invention is formed on a surface of the support layer 330 opposite to the radiation medium layer 320 with a removal groove 331 corresponding to the scattering line removal pattern 340 And filling the removal groove 331 with a radiation shielding material. Here, the removal groove 331 can be formed by physical processing by a fine saw blade or by laser processing. In the present invention, lead (Pb) is applied as a radiation shielding material to be filled in the removal groove (331). Other shielding materials such as Bismuth, Barium, and Tungsten may also be used as radiation shielding materials.

The depth of the removing groove 331 for forming the scattering line removing pattern 340, that is, the thickness of the scattering line removing pattern 340, may be determined based on the size of the sensing pixel and the lattice ratio. 6, the lattice ratio is defined as the ratio of the pitch of the lattice to the thickness of the shielding pattern. The pitch D of the lattice in the scattering line removing pattern 340 according to the present invention is the ratio The thickness h of the scattering line removal pattern 340, that is, the depth h of the removal groove 331, can be determined when the grid ratio is determined.

According to the above configuration, after the radiation irradiated from the irradiation part 10 is incident on the patient, the transmission line 1 and the scattering line 3 are directed to the digital radiation detector 300 according to the present invention. Here, the transmission line 1 having a straight line passes between the scattering line removing patterns 340 formed on the supporting layer 330 and is incident on the radiation medium layer 320. On the other hand, even if the scattering line 3 is incident between the scattering line removing patterns 340, the scattering line removing pattern 340 can be absorbed by the scattering line 3.

At this time, the remaining region of the support layer 330 through which the transmission line 1 is to be transmitted, other than the scattering line removal pattern 340, The transmission line 1 whose transmission is blocked by the scattering line removal pattern 340 does not reach the effective response area VSA even if it is straight ahead as a result, The image loss due to the line removal pattern 340 does not occur.

That is, the scattering line elimination pattern 340 forms a transmissive region corresponding to the plurality of sensing pixels, so that the scattering line elimination pattern 340 for removing the scattering line 3 forms a radiation image Only the scattering line 3 is removed without any influence on the scattering line 3.

In addition, the removal grooves adjacent to each other in the digital radiation detector 300 according to the present invention may be formed parallel to each other in the vertical direction as shown in FIG. In the case of the conventional scattering line eliminating grating 20, there is a case where the grating pattern has a shape radially spreading in the up and down direction. This is because the conventional scattering line eliminating grating 20 and the digital radiation detector 30 are separated from each other So as to correspond to the radiation emitted from the irradiation part 10. Therefore, in the fabrication of the conventional scattering line eliminating grating 20, the angle of the grating pattern in the vertical direction is different as the distance from the center is made, If the angle is not changed, the image may be adversely affected.

On the other hand, in the case of the digital radiation detector 300 according to the present invention, since the scattering line removing pattern 340 is located close to the sensing substrate layer 310, the scattering line removing pattern 340 is vertically, So that it is not only easy to manufacture but also applicable irrespective of the distance from the irradiation part 10.

The conventional scattering line removing grating 20 shields a part of the transmission line 1 regardless of the position of the sensing pixel and transmits the transmission line 1 toward the sensing pixel, The scattering line removal pattern 340 according to the present invention is formed in the boundary region of the sensing pixel, that is, in the non-sensing region, so that the transmission line 1) It is possible to reduce the image loss due to shielding, and consequently to reduce the dose of radiation.

In addition, since the scattering line removal pattern 340 according to the present invention does not affect the formation of the image, the use of the conventional scattering line removal grating 20 eliminates the scattering line removal It is possible to eliminate the structure of reciprocating the grating 20 in the plate surface direction, so that the structure can be simplified and the size of the product can also be reduced.

7 (a), in the case of the conventional radiological examination apparatus, there is a problem that the sharpness is reduced due to the provision of the scattering line removal grating 20 between the patient and the digital radiation detector 300, The digital radiation detector 300 according to the present invention is directly applied to the lower portion of the patient and the distance d2 from the radiation applying unit 10 to the digital radiation detector 300 is set to be shorter, (D1) of the conventional radiographic inspection apparatus, thereby improving the sharpness under the same conditions and consequently reducing the surface dose of the patient.

8 is a diagram illustrating simulation results for verifying the effect of the digital radiation detector 300 according to the present invention. 8B shows the result when the conventional scattering line removing grating 20 is used and FIG. 8C shows the result when the scattering line removing grating 20 shown in FIG. 8 is not used. FIG. Is a result of using the digital radiation detector 300 according to the present invention.

Simulation was carried out using Monte Carlo simulation tool MCNPX 2.6.0. The scattering line (3) and the transmission line (1) transmission factor, which are used to compare the performance of the lattice, , But the surface dose of the patient was decreased by more than 10%. Also, as shown in Fig. 8, it can be confirmed that the contrast is improved visually.

While the present invention has been described in connection with what is presently considered to be practical exemplary embodiments, it is to be understood that the invention is not limited to the disclosed embodiments, but, on the contrary, It will be clear to those who have knowledge.

300: Digital radiation detector 310: Inspection substrate layer
320: Radiation medium layer 330: Support layer
331: removal groove 340: scattering line removal pattern
10:

Claims (8)

A radiation-sensitive layer responsive to radiation,
A sensing substrate layer having a plurality of sensing pixels coupled to one surface of the layer of radiation to sense the response of the layer of radiation,
A support layer coupled to the other surface of the radiation medium layer to protect the radiation medium layer;
A scattering line removing pattern formed on the supporting layer to shield the scattering line;
Wherein the surface of the sensing substrate layer facing the radiation medium layer includes at least one area of each sensing pixel, and includes an effective sensing area for sensing a response of the radiation sensing layer, and a non-sensing area other than the effective sensing area ;
Wherein the scattering line elimination pattern is formed in a pattern corresponding to the no-excitation region.
The method according to claim 1,
A removal groove corresponding to the scattering line removal pattern is formed on a surface of the support layer opposite to the radiation medium layer;
Wherein the scattering line removal pattern is formed by filling the removal groove with a radiation shielding material.
3. The method of claim 2,
The non-
A data line formed in a first direction to be connected to the plurality of sensing pixels,
And a plurality of voltage lines spaced apart from each other in a first direction intersecting the first direction to be connected to the plurality of sensing pixels;
Wherein the scattering line removal pattern is formed in a pattern corresponding to at least one of the plurality of data lines and the plurality of voltage lines.
3. The method of claim 2,
Wherein the support layer is made of graphite or aluminum;
Characterized in that the shielding material comprises a lead material.
3. The method of claim 2,
Wherein the depth of the removal groove is determined based on a size of the sensing pixel and a predetermined lattice ratio.
3. The method of claim 2,
The radiation medium layer comprising a photoconductor responsive to radiation to produce a charge signal;
Wherein each sensing pixel of the sensing substrate layer senses the charge signal.
3. The method of claim 2,
Wherein the radiation medium layer comprises a scintillator responsive to radiation to generate light;
Wherein each of the sensing pixels of the sensing substrate layer senses light from the scintillator.
3. The method of claim 2,
And the removal grooves adjacent to each other are formed parallel to each other in the vertical direction.
KR1020140021799A 2014-02-25 2014-02-25 Digital radiation detector KR101684730B1 (en)

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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000512084A (en) * 1997-04-02 2000-09-12 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ X-ray apparatus having a sensor matrix
JP2002529712A (en) * 1998-10-29 2002-09-10 ディレクト レディオグラフィ コーポレーション Anti-scatter radiation grid with detectors for detectors
JP2011101686A (en) * 2009-11-10 2011-05-26 Shimadzu Corp Radiographic apparatus
JP2011218147A (en) * 2010-03-26 2011-11-04 Fujifilm Corp Radiographic system

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2001061101A (en) * 1999-08-23 2001-03-06 Fuji Photo Film Co Ltd Image processing method and system
JP2009195512A (en) * 2008-02-22 2009-09-03 Fujifilm Corp Radiation image processing apparatus

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000512084A (en) * 1997-04-02 2000-09-12 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ X-ray apparatus having a sensor matrix
JP2002529712A (en) * 1998-10-29 2002-09-10 ディレクト レディオグラフィ コーポレーション Anti-scatter radiation grid with detectors for detectors
JP2011101686A (en) * 2009-11-10 2011-05-26 Shimadzu Corp Radiographic apparatus
JP2011218147A (en) * 2010-03-26 2011-11-04 Fujifilm Corp Radiographic system

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