WO2008131825A1 - Röntgengerät sowie detektionseinheit für ein röntgengerät - Google Patents
Röntgengerät sowie detektionseinheit für ein röntgengerät Download PDFInfo
- Publication number
- WO2008131825A1 WO2008131825A1 PCT/EP2008/001815 EP2008001815W WO2008131825A1 WO 2008131825 A1 WO2008131825 A1 WO 2008131825A1 EP 2008001815 W EP2008001815 W EP 2008001815W WO 2008131825 A1 WO2008131825 A1 WO 2008131825A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- detection unit
- detectors
- ray
- detector
- unit according
- Prior art date
Links
- 238000001514 detection method Methods 0.000 title claims description 89
- 230000005855 radiation Effects 0.000 claims abstract description 35
- 239000011888 foil Substances 0.000 claims description 17
- 238000003384 imaging method Methods 0.000 claims description 7
- -1 polyethylene terephthalate Polymers 0.000 claims description 5
- 239000000463 material Substances 0.000 claims description 4
- 230000035515 penetration Effects 0.000 claims description 4
- 229910052751 metal Inorganic materials 0.000 claims description 3
- 239000002184 metal Substances 0.000 claims description 3
- 229910052709 silver Inorganic materials 0.000 claims description 3
- 239000004332 silver Substances 0.000 claims description 3
- 238000003491 array Methods 0.000 claims description 2
- 230000001678 irradiating effect Effects 0.000 claims description 2
- 229920000139 polyethylene terephthalate Polymers 0.000 claims description 2
- 239000005020 polyethylene terephthalate Substances 0.000 claims description 2
- 230000004044 response Effects 0.000 claims description 2
- 239000002985 plastic film Substances 0.000 claims 1
- 229920006255 plastic film Polymers 0.000 claims 1
- 210000002455 dental arch Anatomy 0.000 description 8
- 238000000034 method Methods 0.000 description 3
- 238000012545 processing Methods 0.000 description 3
- OAICVXFJPJFONN-UHFFFAOYSA-N Phosphorus Chemical compound [P] OAICVXFJPJFONN-UHFFFAOYSA-N 0.000 description 2
- 230000008901 benefit Effects 0.000 description 2
- 238000002591 computed tomography Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000005281 excited state Effects 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 230000005284 excitation Effects 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 210000001847 jaw Anatomy 0.000 description 1
- 239000011159 matrix material Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000002245 particle Substances 0.000 description 1
- 230000000149 penetrating effect Effects 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 230000001681 protective effect Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 238000010561 standard procedure Methods 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 238000013519 translation Methods 0.000 description 1
Classifications
-
- A61B6/51—
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4233—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
Definitions
- the invention relates to an X-ray device with
- an X-ray source for irradiating an object, which is movable by means of a first drive means along a trajectory;
- a detection unit which is incident on X-ray radiation after penetration of the object and which is movable by means of a second drive means along a detection trajectory.
- the invention relates to a detection unit for an X-ray machine with at least one at least two-dimensionally resolving detector with a radiation-sensitive surface.
- the detection unit usually comprises an integrating, two-dimensional resolution detector with a planar radiation-sensitive surface, which may be, for example, a digitally readable storage film, a CCD sensor or a CMOS sensor.
- the X-ray source and the detection unit are simultaneously moved about a common pivot point, wherein the ratio of the distance of the pivot point to the detector to the distance of the pivot point to the X-radiation source remains the same.
- the X-ray source and the detection unit when rotated, move in opposite directions on parallel rectilinear paths, wherein the fulcrum is displaced on a path parallel to the paths of the X-ray source and the detection unit.
- the detector is arranged so that its planar surface facing the radiation source is parallel to the path of the detection unit, and the X-radiation source is rotated in accordance with the position of the detection unit so that the X-radiation after penetrating the object to be irradiated on the detection unit or the detector meets.
- a medical application of the x-ray device is a body part of a patient, especially in the case of a dental application of the x-ray device around the patient's dental arch.
- Each individual recording is assigned to a narrow, planar projection area in which the tissue penetrated by the X-ray radiation of a patient is sharply displayed.
- narrow vertical areas of individual images are joined together.
- focal plane which is parallel IeI is to the movement plane of the detection unit and X-ray radiation source and contains the fulcrum, sharply imaged.
- Levels parallel to this focal plane are blurred or blurred with increasing distance to the focus plane and with increasing tilt angle.
- computed tomography was developed in which the X-ray source and the detection unit are rotated by 180 ° around the object and an X-ray image is acquired for each angular step of the rotation. From the large number of two-dimensional X-ray images recorded in this way, the three-dimensional data of the X-ray density can be determined by means of a computation-intensive method.
- the object of the invention is to provide an X-ray device and a detection unit for an X-ray device to provide, through which relatively high X-ray dose several high-resolution sectional images can be generated, the computational effort remains low.
- the detection unit comprises at least two detectors, which
- the detectors each absorb only a portion of the incident on them X-ray radiation.
- At least two detectors are provided, which are arranged such that the surfaces of the detectors are parallel to each other;
- the detectors only partially absorb x-radiation.
- the radiation-sensitive surfaces of the detectors are arranged one behind the other in the direction of radiation.
- the position of the focal plane in which sharp is imaged at given acquisition parameters which include the tube voltage, the exposure time, the beam current and the beam cross-section count, from the distance of the detector to the radiation source.
- each detector must be assigned a focal plane which is at a distance from the focal plane of another detector.
- FIG. 1 is a plan view of a schematically illustrated X-ray apparatus
- Figure 2 is a perspective view of the X-ray apparatus of Figure 1;
- FIG. 3 shows a first exemplary embodiment of a sensor unit
- FIG. 4 shows a second exemplary embodiment of a sensor unit
- Figure 5 is a diagram for illustrating a possible
- Figure 6 is a representation corresponding to Figure 5, wherein a detection unit is shown with five detectors;
- FIG. 7 shows a diagram in which the decrease in the intensity of the X-ray radiation is qualitatively shown as a function of how many detectors the x-ray radiation has already penetrated.
- FIG. 8 shows a schematic representation of the imaging conditions when imaging a circular-arc-shaped section of a jaw.
- an X-ray machine is denoted overall by 10.
- the X-ray device 10 comprises an X-ray source 12 and a detection unit 14, which are supported by a movable linkage 16.
- the latter is movable by means of a hydraulic cylinder 18 with a piston rod 20 in the z-direction, wherein the hydraulic cylinder 18 is fixed to a building wall, not shown here or a corresponding frame.
- the z-axis coincides with the axis of the piston rod 20, the x-axis and the y-axis are fixed in space.
- the piston rod 20 carries at its free end a double joint 22.
- a first joint part 24 of the double joint 22 is rotatable about the z-axis by an electric motor 26 and rigidly connected via an inner support rod 28 to a first joint part 30 of an arm joint 32.
- a second joint part 34 of the arm joint 32 is rotatable about the z-axis via an electric motor 36 and rigidly connected to a first joint part 40 of an end joint 42 via an outer support rod 38.
- a second joint part 46 of the end joint 42 that can be rotated about the z-axis via an electric motor 44 carries the detection unit 14.
- a second main arm 48 has the same components as the main arm 48; these are identified in FIGS. 1 and 2 by corresponding reference symbols plus a comma.
- the second joint part 46 'of the end joint 42' carries the X-ray source 12.
- the X-ray source 12 and the detection unit 14 are located substantially at the same height in a common xy plane, for which the components 24 'to 46' of the main arm 48 'opposite the corresponding components of the main arm 48 with the same vertical dimensions top and bottom are reversed ,
- the electric motors 26, 36, 44 and 26 ', 36', 44 ' via lines 50, 52, 54 and 50', 52 ', 54' connected to a control / computing unit 56 .
- the X-ray source 12 communicates via a line 58 with the control / computing unit 56, so that on the latter recording parameters, such as the tube voltage, the exposure time, the beam current and the beam cross section for the X-ray source 12 can be adjusted.
- the corresponding parameters can be entered into the control / computation unit 56 by means of a keypad 55.
- the control / computing unit 56 is also connected via a line 60 to a control valve, not shown here, via which a pressure medium pump can be connected to the hydraulic cylinder 18, whereby the position of the cylinder rod 20 is adjustable and the position of the linkage 16 on the z -Axis can be adjusted.
- the X-ray apparatus 10 also includes a light unit 94, which will be explained in more detail below.
- FIG. 3 shows an exemplary embodiment of the sensor unit 14. This includes a housing 62 of visible light opaque and X-ray transmissive material. An upper cover wall 64 is shown partially broken away.
- a side wall 66 which is perpendicular to the top wall 64, has five slots 68 which are protected against the penetration of light and which are uniformly spaced apart from one another and extend perpendicularly to the top wall 64.
- guide grooves 72 are provided on the side wall 70, which is parallel to the side wall 66, on the top wall 64 and on the side wall, which is parallel thereto and not visible in FIG provided, on the inside of the top wall 64 mounted further guide grooves for clarity are not shown.
- the Detekttorfolien 74 have a plane facing the radiation source surface 75 and are made of such a material that they do not completely, but only partially absorb X-rays incident on them, which will be explained in more detail below.
- imaging films contain phosphor particles with color centers, which can be brought into a stable excitation state by X-ray light. By scanning with a reading laser beam can bring the excited states in a higher excited state, which relaxes quickly with the emission of fluorescent light. By detecting the latter, the latent image of a storage film can thus be read out.
- FIG. 4 shows a detection unit 14 corresponding to FIG. 3, in which 74 CCD or CMOS detectors 76 are inserted instead of the detector foils.
- the detectors 76 may be conventional visible light responsive CCD or CMOS detectors provided with an X-ray (partially) absorbing phosphor layer or disposed behind a respective fluorescent screen.
- the detector films 74 and detectors 76 are arranged one behind the other staggered in the detection unit 14, that their levels under conditions of use pointing to the X-ray source
- control / computation unit 56 When using CCD or CMOS detectors 76, these are connected to the control / computation unit 56 via a multi-core data line cable 78, which is shown dotted in FIGS. 1 and 2.
- the control / computation unit 56 When the control / computation unit 56 receives the data, it may either directly evaluate the data and generate a two-dimensional image for each detector 76, or the data may be passed from the control / computation unit 56 to an external computer for evaluation herein not shown.
- the data cable 78 may also be replaced by a wireless communication link, e.g. an infrared data link, a Bluetooth data link or the like.
- Side wall of the housing 62 which is designated in Figures 3 and 4 by the reference numeral 80, consists of a material which absorbs only a small amount of X-radiation, such.
- a thin blackened sheet of polyethylene terephthalate or a thin Metal film of a metal of low atomic number As a thin blackened sheet of polyethylene terephthalate or a thin Metal film of a metal of low atomic number.
- the side wall 80 of the housing 62 can also be completely dispensed with.
- detector films X-ray films or image plates
- a visible light-impermeable protective cover X-ray films or image plates
- the housing 62 can also be designed to accommodate more or less than 5 detector foils 74 or detectors 76.
- 3 detector foils 74 or detectors 76 are contemplated, but also 7, 9 and more detectors 74 and 76 as well as an intervening number can be used.
- FIGS. 5 and 6 show a possible mode of operation of the X-ray apparatus 10 using a detection unit 14 with three detectors 74A, B, C or 76A, B, C on the one hand (FIG. 5) and five detectors 74A, B, C, D, E or 76A, B, C, D, E on the other hand ( Figure 6).
- a circular-arc-shaped section of a dental arch 82 of a patient which is also shown in FIG. 1, is shown as an object to be transilluminated.
- the X-ray source 12 is shown in three different positions RA, RB and RC. These three positions are traversed by the X-ray source 12 during a recording by the main arm 48 'of the linkage 16 so by means of the electric motors 26' and 36 'is moved, that the X-ray source 12 along a rectilinear radiation source trajectory moves 86.
- the detection unit 14 in turn is moved by a corresponding control of the electric motors 26 and 36 by means of the main arm 48 during a recording in opposite directions to the movement of the X-ray source 12 along a rectilinear detection unit trajectory 88.
- the detection unit 14 is rotated during movement along the path 88 about the z-axis such that the radiation-sensitive surface 75 or 77 of the detector foils 74 or detectors 76 extending in each xz plane is always parallel to the path of travel 88 is aligned. This can be clearly seen in FIGS. 5 and 6.
- Three detector foils 74A, 74B, 74C3 arranged behind it are then rotated during the movement of the X-ray source 12 about the dental arch 82 both with the rotation angle of the X-radiation source 12 and linearly displaced with respect to the X-ray gap 100, as shown in FIG. 8 for three exposure positions ,
- an approximately circular arc-shaped section of a dental arch 82 is assumed, and the X-ray radiation source 12 is moved at a fixed distance from a cylindrical focal surface within the dental arch. moves so that it is always perpendicular to this focus area.
- Three detector foils 74A, 74B and 74C are also held with the X-ray gap 100 at a fixed distance from the associated focus area 9OA, 9OB, 9OC and pivoted by the same angle.
- the pivot point 92 is located in the center or center of curvature of the focus surfaces 9OA, 9OB and 9OC, which are sharply imaged on the detector films 74A, 74B and 74C.
- the storage film 74 is displaced by an angle w such that, e.g. the point Pl in the point Pl ', the point P2 passes into the point P2'.
- the associated focus surface 9OC moves outward.
- the entire movement of X-ray source 12 and detection unit 14 is matched to one another during a recording so that, as mentioned above, narrow vertical recording areas of individual images on the detectors 74 and 76 are combined to form an overall image.
- three detector foils 74A, 74B and 74C are provided in the detection unit 14 in FIG. 5.
- the sectional planes imaged thereon correspond to the focal planes 9OA, 9OB and 9OC respectively shown by a solid line.
- the focal planes 9OA, 9OB and 9OC are arranged one after the other according to the arrangement of the detector foils 74A, 74B, 74C within the detection unit 14.
- the distance d between the focal planes 9OA and 9OB or 9OB and 9OC is dependent on the arrangement of both the X-ray source 12 and the detection unit 14 or the detector films 74 received therein relative to each other.
- the distance d between two adjacent focal planes 90 can be determined as follows: If a is the distance between the central detector film 74B and the fulcrum 92, b is the distance between the X-ray source 12 and the fulcrum 92, and c is the distance between two adjacent detector films 74A, 74B and 74B, 74C, then the distance is calculated d between two adjacent focal planes 9OA, 9OB and 9OB, 9OC, respectively
- the position of the X-ray radiation source 12 which is used to calculate the position and the distance d of the focal plane 90 or to determine the distance b is understood to be the average origin of the X-ray radiation, for example the average location of an X-ray cathode.
- the X-ray source 12 is shown schematically as a circular cylinder, it being assumed that the average location of the formation of the X-radiation is in the axial center of the circular cylinder.
- FIG. 6 shows the arrangement with a detection unit 14, which uses five detector foils 74A to 74E.
- the detection unit 14 has an additional memory film 7492 arranged closer in the direction of the X-ray radiation source 12 and an additional detector film 74E provided on the opposite side of the detection unit 14.
- a focus plane 9OA, 9OB, 9OC, 9092 and 9OE are respectively sharply imaged on the detector films 74A to 74E, of which two neighboring focal planes 90 are present at a distance d from each other, which is calculated in accordance with the formula given above.
- the calculation of the distance d explained using the example of the detector films 74 is carried out analogously in the case of CCD or CMOS detectors 76. To determine the distances a and b while the position of the radiation-sensitive surface 77 is taken as a reference.
- the x-ray density of the object can be sharply focused on the respective detector films 74 with only one image in a plurality of successive focal planes 90 respectively.
- Imaging detectors 76 The dose required for this is, for example, in the case of a dental, intraoral X-ray, which is illustrated here using the example of the dental arch 82, in the same order of magnitude as in a standard intraoral single image.
- the transmitted by a detector film 74 and a detector 76 X-ray radiation reaches behind the detector films 74 and detectors 76, so that at the same radiation exposure sectional images corresponding to the number the detector films 74 or detectors 76 used can be generated.
- Figure 7 is a graph showing the decrease in intensity of X-ray in a stack of ten standard intraoral detector films at a tube voltage of 70 kV, which corresponds to about 35 keV average X-ray energy.
- the X-radiation is also present after penetration of a plurality of detector foils with relatively high intensity, which is sufficient to produce an image on a respective following detector foil.
- Out of focus planes 90 levels are shown blurred on the detectors 74 and 76, respectively.
- the acquired cross-sectional images can be post-processed after the digital readout with a conventional image processing, which subtracts the average X-ray density from those image planes, which is outside the focal plane 90 associated with the corresponding detector film 74.
- the image processing is carried out automatically by the control / processing unit 56 or, as mentioned, by an external computer.
- the above-mentioned lighting unit 94 is attached to the double joint 22 at the level of the X-ray radiation source 12 and the detection unit 14. In accordance with the number of detectors 74 and 76 used, it linearly emits light in each case in an xz plane onto the object 82, For example, by means of a respective light-emitting diode array 96th
- the distance between two xz planes to be assigned to each one light beam and their position corresponds to the distance d between the focal planes 90 or the position of the focal planes 90.
- reference lines may be projected onto the outer contour of the object 82 to align the object 82 prior to x-ray exposure according to the location of the focal planes 90.
- the individual light-emitting diode arrays 96 can be moved by means of electric motors 98 on the y-axis, and when using different detection units 14, in which the distance c between the detectors 74 and 76 is different, are positioned according to the calculated distance d to each other.
- the detection unit 14 comprises at least two of the following detector types: silver halide films, Image plates, image converter-based detectors.
- the detection unit 14 comprises at least two detector sheets 74 and / or detectors 76 which differ in response to the X-rays emitted by the X-ray source 12.
- the X-ray cross-section of the detectors preferably increases in the beam direction.
- the increase in the cross-section is chosen so that the amount of X-ray light absorbed in the detectors is substantially the same, the images produced by the detectors will have substantially the same density and contrast.
- a servo drive is provided for at least one of the detectors of the detection unit, which additionally moves the detector parallel to the detector plane or antiparallel to it when moving along the detection path, then the position of the associated focal plane can be influenced.
- the additional movement is preferably proportional to the path of the detection unit 14.
- the additional movement is also proportional to the distance of the detector under consideration from the center of the detection unit seen in the beam direction.
Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CN200880014197A CN101686823A (zh) | 2007-04-30 | 2008-03-07 | X射线设备以及用于x射线设备的检测单元 |
EA200901450A EA200901450A1 (ru) | 2007-04-30 | 2008-03-07 | Рентгеновский аппарат и детекторный узел для него |
EP08716330A EP2150178A1 (de) | 2007-04-30 | 2008-03-07 | Röntgengerät sowie detektionseinheit für ein röntgengerät |
US12/596,247 US20100150316A1 (en) | 2007-04-30 | 2008-03-07 | X-ray apparatus and detection unit for an x-ray apparatus |
JP2010504474A JP2010524603A (ja) | 2007-04-30 | 2008-03-07 | X線装置、及びx線装置用検出部 |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE102007020642.0 | 2007-04-30 | ||
DE102007020642A DE102007020642A1 (de) | 2007-04-30 | 2007-04-30 | Röntgengerät sowie Sensoreinheit für ein Röntgengerät |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2008131825A1 true WO2008131825A1 (de) | 2008-11-06 |
Family
ID=39595826
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/EP2008/001815 WO2008131825A1 (de) | 2007-04-30 | 2008-03-07 | Röntgengerät sowie detektionseinheit für ein röntgengerät |
Country Status (7)
Country | Link |
---|---|
US (1) | US20100150316A1 (de) |
EP (1) | EP2150178A1 (de) |
JP (1) | JP2010524603A (de) |
CN (1) | CN101686823A (de) |
DE (1) | DE102007020642A1 (de) |
EA (1) | EA200901450A1 (de) |
WO (1) | WO2008131825A1 (de) |
Families Citing this family (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FI121647B (fi) * | 2009-07-01 | 2011-02-28 | Palodex Group Oy | Hammasröntgenlaitteen liikemekanismi |
DE102009060019B4 (de) * | 2009-12-21 | 2017-05-24 | DüRR DENTAL AG | Detektionseinheit für Prüfstrahlen sowie Ausleseeinheit und Untersuchungsgerät mit einer solchen |
KR101600609B1 (ko) * | 2014-05-23 | 2016-03-21 | (주)제노레이 | 엑스선 촬영장치의 정렬 바이트 및 이를 갖는 엑스선 촬영장치 |
WO2016018002A1 (ko) * | 2014-07-28 | 2016-02-04 | 주식회사바텍 | 엑스선 영상 촬영장치 및 엑스선 영상 촬영방법 |
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US4845731A (en) * | 1985-06-05 | 1989-07-04 | Picker International | Radiation data acquistion |
US5548123A (en) * | 1994-12-06 | 1996-08-20 | Regents Of The University Of California | High resolution, multiple-energy linear sweep detector for x-ray imaging |
EP0842637A1 (de) | 1996-11-15 | 1998-05-20 | Philips Patentverwaltung GmbH | Verfahren zur Steuerung eines koppelstangenlosen Tomographiegerätes |
EP1004272A1 (de) | 1998-11-25 | 2000-05-31 | Picker International, Inc. | Tomographische Bilderzeugung mittels eindringender Strahlung |
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US4211927A (en) * | 1978-11-24 | 1980-07-08 | Cgr Medical Corporation | Computerized tomography system |
FR2461279B1 (fr) * | 1979-07-11 | 1987-01-02 | Fuji Photo Film Co Ltd | Procede de traitement d'une image radiographique |
US4581535A (en) * | 1981-10-16 | 1986-04-08 | Fuji Photo Film Co., Ltd. | Method of recording X-ray image |
JPS6170547A (ja) * | 1984-09-13 | 1986-04-11 | Fuji Photo Film Co Ltd | 放射線画像情報読取方法 |
US4792900A (en) * | 1986-11-26 | 1988-12-20 | Picker International, Inc. | Adaptive filter for dual energy radiographic imaging |
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EP1619549A3 (de) * | 2004-07-23 | 2009-11-04 | Konica Minolta Medical & Graphic, Inc. | Gerät zur Aufnahme medizinischer Bilder und Kassette zur Aufnahme von medizinischen Röntgenbildern |
-
2007
- 2007-04-30 DE DE102007020642A patent/DE102007020642A1/de not_active Withdrawn
-
2008
- 2008-03-07 EA EA200901450A patent/EA200901450A1/ru unknown
- 2008-03-07 WO PCT/EP2008/001815 patent/WO2008131825A1/de active Application Filing
- 2008-03-07 CN CN200880014197A patent/CN101686823A/zh active Pending
- 2008-03-07 JP JP2010504474A patent/JP2010524603A/ja not_active Withdrawn
- 2008-03-07 EP EP08716330A patent/EP2150178A1/de not_active Withdrawn
- 2008-03-07 US US12/596,247 patent/US20100150316A1/en not_active Abandoned
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US5548123A (en) * | 1994-12-06 | 1996-08-20 | Regents Of The University Of California | High resolution, multiple-energy linear sweep detector for x-ray imaging |
EP0842637A1 (de) | 1996-11-15 | 1998-05-20 | Philips Patentverwaltung GmbH | Verfahren zur Steuerung eines koppelstangenlosen Tomographiegerätes |
EP1004272A1 (de) | 1998-11-25 | 2000-05-31 | Picker International, Inc. | Tomographische Bilderzeugung mittels eindringender Strahlung |
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See also references of EP2150178A1 |
Also Published As
Publication number | Publication date |
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CN101686823A (zh) | 2010-03-31 |
DE102007020642A1 (de) | 2008-11-06 |
US20100150316A1 (en) | 2010-06-17 |
EA200901450A1 (ru) | 2010-04-30 |
JP2010524603A (ja) | 2010-07-22 |
EP2150178A1 (de) | 2010-02-10 |
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