EP1089297B1 - Gitter zur Absorption von Röntgenstrahlung - Google Patents

Gitter zur Absorption von Röntgenstrahlung Download PDF

Info

Publication number
EP1089297B1
EP1089297B1 EP00203370A EP00203370A EP1089297B1 EP 1089297 B1 EP1089297 B1 EP 1089297B1 EP 00203370 A EP00203370 A EP 00203370A EP 00203370 A EP00203370 A EP 00203370A EP 1089297 B1 EP1089297 B1 EP 1089297B1
Authority
EP
European Patent Office
Prior art keywords
comb
grid
elements
ray
radiation
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
EP00203370A
Other languages
German (de)
English (en)
French (fr)
Other versions
EP1089297A3 (de
EP1089297A2 (de
Inventor
Peter Flisikowski
Stefan Dr. Schneider
Josef Dr. Lauter
Herfried Dr. Wieczorek
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Philips Intellectual Property and Standards GmbH
Koninklijke Philips NV
Original Assignee
Philips Intellectual Property and Standards GmbH
Koninklijke Philips Electronics NV
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Philips Intellectual Property and Standards GmbH, Koninklijke Philips Electronics NV filed Critical Philips Intellectual Property and Standards GmbH
Publication of EP1089297A2 publication Critical patent/EP1089297A2/de
Publication of EP1089297A3 publication Critical patent/EP1089297A3/de
Application granted granted Critical
Publication of EP1089297B1 publication Critical patent/EP1089297B1/de
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • 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

Definitions

  • the invention relates to a grating with electromagnetic radiation absorbing combing elements serving for grating.
  • Such gratings are used as scattered radiation gratings in X-ray technology in order to absorb stray radiation arising in the tissue of the patient before the characteristic X-ray signal resulting from the different weakening properties of the examined tissue strikes the X-ray detector.
  • US 3988589 discloses a collimator constructed of interdigitated elements with a double comb structure.
  • a collimator sintered beam grid
  • the collimator is formed by an X-ray absorbing frame in which first and second partition plates are arranged.
  • the partition plates each have longitudinal slots to the partition plate, which make it possible to insert the first partition plates in a corresponding angle in the second partition plates.
  • the rectangular frame has slots at its inner edges which serve to receive the respective ends of the partition plates.
  • X-ray radiation emitted by an X-ray source passes through the patient and is correspondingly weakened by the different density and chemical composition of the tissue or bones to be examined.
  • the X-ray signal is subject to scattered radiation.
  • the X-radiation passes through a scattered radiation grid focused on the focus of the radiation source.
  • CT scanners are designed so that the radiation source faces the detector on a gantry that rotates around the patient, moving the patient slowly with a cot. Vibrations of the gantry, which are also transmitted to the scattered beam grid and the X-ray detector, have a negative effect on the image quality of the image to be displayed. Such negative effects can not be reproduced, so that a subsequent reduction of these image distorting effects in image processing is only possible to a limited extent.
  • the object of the invention is therefore to provide a scattered radiation grating for reducing the scattered radiation, which by means of simple production with a corresponding robustness can also be realized for large-area scattered-beam gratings.
  • a scattered radiation grid is arranged above the X-ray detector in such a way that the primary X-ray radiation impinges through the grid onto a respective detector element arranged underneath.
  • Scattering gratings may be composed of comb-absorbing comb elements having several comb structures fixed by a frame.
  • the comb elements have a preferably rectangular basic shape and have comb webs which are arranged transversely to the surface of a base plate and the comb base surface formed thereby. These comb webs form the comb structure.
  • the comb webs are focused on the focus of the radiation source, whereby the distance between the comb webs at the upper edge of the comb element is less than at the lower edge.
  • a plurality of these comb elements are arranged such that the comb webs extending transversely to the comb base surface abut or abut the nearest comb element with the associated comb base surface. This creates a two-dimensional lattice structure.
  • the distance between the comb webs and the depth of the comb webs determines the resolution of the scattered beam grid. This two-dimensional grid is aligned with the grid openings in the direction of the incident X-radiation.
  • the side edges of the individual comb elements are fastened in the frame by means of grooves.
  • the number of comb elements to be joined is determined by the size of the x-ray detector used.
  • the X-ray detector is usually many times longer in CT devices than it is wide. It proves to be advantageous that the comb elements have a high degree of robustness and stability, which allows many comb elements to be arranged in a frame, so that a large-area scattered-beam grid is thereby formed which covers a large-area X-ray detector.
  • the X-ray radiation characteristic of the examined region is converted, for example, into light in an X-ray detector, which is either read out by a photosensitive sensor or which exposes a film accordingly.
  • sensors read the image information.
  • the X-ray quanta of a corresponding examination area to be imaged on an image pixel be converted only in the associated detector element and in the corresponding underlying Sensor is detected.
  • Due to the scattered beam grid the X-ray quanta characteristic of an examination area corresponding to the resolution of the detector reach the corresponding detector element directly in the corresponding grid opening.
  • the X-ray quanta which are characteristic for an investigation area corresponding to the resolution of the detector, are conducted through the scattered radiation grid in the corresponding grid opening directly to the associated detector element.
  • the scattering scattered radiation is absorbed by the lattice structure of the scattered radiation grid.
  • the scattered beam grid is formed of comb elements with a double comb structure and planar lamellae.
  • the comb elements have ridge webs standing transversely to the base plate on both sides of the base plate.
  • the comb webs are at these Doppelkammimplantationn transverse to the two Kammbasis vom on both sides of the base plate.
  • a double comb element and a flat lamella are alternately lined up. This also creates a grid.
  • the double comb elements and the slats are held by the frame.
  • the comb webs of the comb elements are focused in their orientation to the focus of the radiation source.
  • the X-rays hit the scattered beam grid at a predetermined angle. Since the direct X-ray radiation is to pass unhindered through the scattered radiation grid, the orientation of the grid must be adapted to the radiation angle. For this purpose, the distances between the comb webs at the upper edge of the comb elements are smaller than the distances between the comb webs at the lower edge of the comb elements.
  • the frame in which the comb elements are fixed is adapted to the shape of the X-ray detector.
  • Grooves are arranged on the inner sides of the frame.
  • the thickness of the grooves corresponds to the wall thickness of the comb elements, so that they are held by the shape of the grooves.
  • the comb elements can be glued in these grooves.
  • the object is also achieved by a detector with a grating according to the invention for absorbing X-ray radiation.
  • the object is achieved with an X-ray machine with a grid arranged in front of the detector for absorbing X-ray radiation.
  • the object is achieved by a method for producing a grid according to the invention.
  • FIG. 1 shows a computer tomograph, with a gantry 1 at the one radiation source 2 is arranged.
  • the X-ray detector 8 with the scattered radiation grating 3 arranged above it is arranged opposite the radiation source 2.
  • a patient 5 is placed lying on a bed 6.
  • the gantry 1 revolves around the patient 5.
  • an examination area 7 is transilluminated from all sides.
  • the patient 5 is pushed in a horizontal direction through the rotating gantry 1, so that a volume image is taken by means of several cross-sectional images.
  • the area which is scanned with one rotation is substantially larger than in the case of single-row X-ray detectors. As a result, the patient 5 can be pushed through the gantry 1 faster.
  • FIG. 2 shows a one-sided comb element 12 in plan view.
  • This one-sided comb element 12 consists of an X-ray absorbing material, for example (brass, molybdenum, tungsten).
  • the comb structure of this comb element 12 is formed by standing at right angles to a base plate 10 comb webs 11.
  • the height of the comb element 12 depends on the specific application. It is a crucial criterion how much surface is irradiated with a scan. The ratio of useful radiation to scattered radiation deteriorates with increasing width of the X-ray irradiated area per scan. Typically, these comb elements 12 are about 2-6 cm high.
  • the width of the comb element 12 or the base plate 10 is determined by the width of the X-ray detector 8.
  • a scattered beam grating 3, as formed from these comb elements 12, must completely cover the X-ray detector 8.
  • the comb elements 12 are wider than in the narrower multi-line or two-dimensional X-ray detectors 8, which are used in computed tomography. With the depth of the comb webs 11 and the distance D between the individual comb webs 11, the pixel size of such a scattered beam grating 3 is formed.
  • the pixel size is about 1x1 to 2x5 mm 2 .
  • comb elements 12 are arranged to the incident X-radiation that the X-rays pass through the lattice openings formed by comb webs 11 and base plate 10.
  • X-rays are emitted from the radiation source 2 with a focus and radiate away from this focus at a radiation angle.
  • the comb webs 11 are aligned or focused in their arrangement on the base plate 11 after this focus. This is in the FIG. 4 shown.
  • the distance D o between the comb webs 11 is at the upper edge of the base plate 10 is less than the distance D u between the comb webs 11 at the bottom of the base plate 10th
  • the X-ray detectors 8 are adapted to a bend in computer tomographs, it is necessary to adjust the anti-scatter grid 3 accordingly.
  • FIG. 3 It is shown that the depth of the comb webs 11 is lower at the upper edge than at the lower edge of the base plate 10. With long X-ray detectors, a piecemeal assembly of small stray beam grating segments is possible.
  • FIG. 6 the juxtaposition of a plurality of one-sided comb elements 12 is shown. Due to the different depth of the comb webs 11 at the top and bottom edge ( Figure 3 ), the scattered radiation grating 3 can be easily adapted to the bending of the X-ray detector 8. In addition, the bending of the scattered beam grating 3 is enforced by the arrangement of the grooves 14 in the frame 13.
  • FIG. 7 the non-inventive arrangement of a plurality of one-sided comb elements 12 in an X-ray shadowing frame 13 is shown.
  • the frame 13 has on its inner side grooves 14 which in FIG. 8 are shown. These grooves 14 receive the side edges of the base plates 10 of the plurality of single-sided comb members 12.
  • the comb elements 12 can be glued or fixed in another conceivable way. A mechanical fixation by pressing the comb elements 12 is also feasible.
  • a non-inventive scattered radiation grating 3 is formed.
  • the comb webs 11 of a base plate 10 adjoin the rear side of a adjacent base plate 10. The length of such a scattered beam grating 3 can be extended by the number of comb elements 12 as desired.
  • FIGS. 9-12 show a two-sided comb element 15 and a scattered beam grid 3 composed of these and laminations 19.
  • FIG. 9 shows a two-sided comb element 15 with a double comb structure. This consists of a base plate 17 on both sides webs 16 and 18 are arranged. The comb webs 16 and 18 are respectively disposed on both sides of the base plate 17 across the comb base formed by the base plate 17. The above explanations for focusing the one-sided comb element 12 are to be applied correspondingly to this two-sided comb element 15. Likewise, the comb webs 16 and 18 at the lower edge of the base plate 17 are deeper than the comb webs 16 and 18 at the upper edge of the base plate 17 to simulate the bending of the X-ray detector 8.
  • FIG. 11 is the composition of flat slats 19 ( Fig. 10 ) and two-sided comb elements 15.
  • two-sided comb elements 15 are arranged alternately with lamellae 19, so that an inventive scattered radiation grating 3 is formed.
  • the length of the scattered radiation grating 3 can be increased by increasing the number of used two-sided comb elements 15 and fins 19.
  • Streptrahlengitter are used in addition to computed tomography for radiology.
  • a curvature of the scattered beam grating 3 is not required, since the X-ray detector 8 is flat.
  • Such scattered beam gratings typically have different dimensions than those previously mentioned. In these applications, however, occur less vibration.
  • the frames of these scattered radiation grids have larger dimensions and also the comb elements 12 or 15 to be used are larger. Due to the very good inherent stability of the comb elements 15 can be covered with this design of a scattered beam grating a very large application area.
  • the comb elements 12 or 15 can be produced, for example, by means of milling, sintering or injection molding. In the injection molding process, it is possible to mix X-ray absorbing materials with a base material.
  • a non-inventive scattered radiation grating 3 can also be formed by juxtaposing two-sided comb elements 15 without lamellae 19 being arranged between them.
  • the comb elements 12 or 15 can also be arranged by means of spacers so that a scattered radiation grid is formed.
  • a scattered beam grid By varying the distances between the comb webs of the comb elements, such a scattered beam grid can be adapted to specific applications.
  • the resolution could be lower, so that here the scattered-beam grid can have larger grid openings.

Landscapes

  • Physics & Mathematics (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Engineering & Computer Science (AREA)
  • General Engineering & Computer Science (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Measurement Of Radiation (AREA)
EP00203370A 1999-10-02 2000-09-26 Gitter zur Absorption von Röntgenstrahlung Expired - Lifetime EP1089297B1 (de)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE19947537 1999-10-02
DE19947537A DE19947537A1 (de) 1999-10-02 1999-10-02 Gitter zur Absorption von Röntgenstrahlung

Publications (3)

Publication Number Publication Date
EP1089297A2 EP1089297A2 (de) 2001-04-04
EP1089297A3 EP1089297A3 (de) 2004-02-04
EP1089297B1 true EP1089297B1 (de) 2008-10-15

Family

ID=7924303

Family Applications (1)

Application Number Title Priority Date Filing Date
EP00203370A Expired - Lifetime EP1089297B1 (de) 1999-10-02 2000-09-26 Gitter zur Absorption von Röntgenstrahlung

Country Status (4)

Country Link
US (1) US6363136B1 (ja)
EP (1) EP1089297B1 (ja)
JP (1) JP2001137234A (ja)
DE (2) DE19947537A1 (ja)

Families Citing this family (33)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10009285A1 (de) * 2000-02-28 2001-08-30 Philips Corp Intellectual Pty Computertomograph zur Ermittlung des Impulsübertrags-Spektrums in einem Untersuchungsbereich
DE10202987A1 (de) * 2002-01-26 2003-07-31 Philips Intellectual Property Gitter zur Absorption von Röntgenstrahlung
EP1634303B1 (en) * 2003-06-01 2008-09-10 Koninklijke Philips Electronics N.V. Anti-scattering x-ray collimator for ct scanners
US20050017182A1 (en) * 2003-07-25 2005-01-27 Siemens Medical Solutions Usa, Inc. Registered collimator device for nuclear imaging camera and method of forming the same
WO2005027143A2 (en) * 2003-09-12 2005-03-24 Philips Intellectual Property & Standards Gmbh Arrangement for collimating electromagnetic radiation
FR2866438B1 (fr) * 2004-02-16 2006-08-11 Agence Spatiale Europeenne Element optique reflecteur, son procede de fabrication, et instrument optique mettant en oeuvre de tels elements
DE102004027158B4 (de) * 2004-06-03 2010-07-15 Siemens Ag Verfahren zur Herstellung eines Streustrahlenrasters oder Kollimators aus absorbierendem Material
DE102004035943B4 (de) * 2004-07-23 2007-11-08 GE Homeland Protection, Inc., , Newark Röntgencomputertomograph sowie Verfahren zur Untersuchung eines Prüfteils mit einem Röntgencomputertomographen
DE602006011805D1 (de) * 2005-04-15 2010-03-11 Toshiba Kk Kollimator für eine Röntgen CT Vorrichtung und Röntgen CT Vorrichtung
JP2009509133A (ja) * 2005-09-19 2009-03-05 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 電磁放射線の選択的吸収のための格子，及びその製造方法
DE102005044650B4 (de) * 2005-09-19 2008-07-10 Siemens Ag Streustahlenraster mit einer zellenartigen Struktur von Strahlungskanälen und Verfahren zur Herstellung eines solchen Streustrahlenrasters
JP4417898B2 (ja) * 2005-09-26 2010-02-17 株式会社東芝 Ｘ線ｃｔ装置の製造方法
US7362849B2 (en) * 2006-01-04 2008-04-22 General Electric Company 2D collimator and detector system employing a 2D collimator
US8086010B2 (en) * 2006-06-30 2011-12-27 Kabushiki Kaisha Toshiba Medical image diagnosis apparatus and the control method thereof
ATE483233T1 (de) * 2006-07-07 2010-10-15 Koninkl Philips Electronics Nv Gitter zur selektiven übertragung elektromagnetischer strahlung mit einem durch selektive lasersinterung erzeugten strukturelement
WO2008104972A1 (en) * 2007-02-26 2008-09-04 Fiberzone Networks Ltd. Optical crossbar switch
JP5616895B2 (ja) * 2008-10-13 2014-10-29 コーニンクレッカ フィリップス エヌ ヴェ 電磁放射線の選択透過のためのグリッドの製造方法および散乱線除去グリッド
JP5148529B2 (ja) * 2009-02-19 2013-02-20 三菱重工業株式会社 放射線コリメータ及びこれを備えた放射線検出器
JP5405866B2 (ja) * 2009-03-24 2014-02-05 株式会社東芝 コリメータ、放射線検出器、及びｘ線ｃｔ装置
DE102009052627B4 (de) * 2009-11-10 2012-07-12 Siemens Aktiengesellschaft Streustrahlungskollimator und Verfahren zur Herstellung eines Streustrahlungskollimators
FR2954127B1 (fr) * 2009-12-22 2015-10-30 Oreal Agent de coloration et/ou de decoloration des fibres keratiniques en deux parties, comprenant un corps gras et un agent sequestrant.
WO2012000694A1 (en) * 2010-06-28 2012-01-05 Paul Scherrer Institut A method for x-ray phase contrast and dark-field imaging using an arrangement of gratings in planar geometry
JP5667798B2 (ja) * 2010-06-29 2015-02-12 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー コリメータモジュール、多列ｘ線検出器及びｘ線ｃｔ装置
CN103222010A (zh) * 2010-10-08 2013-07-24 海龟湾合伙有限责任公司 三维聚焦防散射栅格及其制造方法
US9048002B2 (en) * 2010-10-08 2015-06-02 Turtle Bay Partners, Llc Three-dimensional focused anti-scatter grid and method for manufacturing thereof
US20120087462A1 (en) * 2010-10-12 2012-04-12 Abdelaziz Ikhlef Hybrid collimator for x-rays and method of making same
JP5674507B2 (ja) * 2011-02-28 2015-02-25 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー ２次元コリメータモジュール、ｘ線検出器、ｘ線ｃｔ装置、２次元コリメータモジュールの組立て方法、および２次元コリメータ装置の製造方法。
DE102011103851B4 (de) * 2011-05-26 2019-05-29 Siemens Healthcare Gmbh Gittermodul eines Streustrahlungsgitters, modulares Streustrahlungsgitter, CT-Detektor und CT-System
US8976935B2 (en) * 2012-12-21 2015-03-10 General Electric Company Collimator grid and an associated method of fabrication
CN104057083B (zh) * 2013-03-22 2016-02-24 通用电气公司 用于制造以高熔点金属材料为基材的零件的方法
DE102014218462A1 (de) * 2014-09-15 2016-03-17 Siemens Aktiengesellschaft Verfahren zur Herstellung eines Kollimatormoduls und Verfahren zur Herstellung einer Kollimatorbrücke sowie Kollimatormodul, Kollimatorbrücke, Kollimator und Tomographiegerät
US9993219B2 (en) * 2015-03-18 2018-06-12 The Board Of Trustees Of The Leland Stanford Junior University X-ray anti-scatter grid with varying grid ratio
CN106226916A (zh) * 2016-07-26 2016-12-14 中国科学院高能物理研究所 光学准直器及其加工方法

Family Cites Families (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3790782A (en) * 1968-03-25 1974-02-05 Hitachi Ltd Topographic radioisotope camera having an adjustable collimator thereon
US3988589A (en) * 1975-07-28 1976-10-26 Engineering Dynamics Corporation Methods of collimator fabrication
US4057726A (en) * 1975-12-22 1977-11-08 G. D. Searle & Co. Collimator trans-axial tomographic scintillation camera
SE423458B (sv) * 1980-09-10 1982-05-03 Agne Larsson Anordning vid en kamera innefattande en manghalskollimator
JPS59152477U (ja) * 1983-03-31 1984-10-12 株式会社島津製作所 シンチレ−シヨンカメラのコンバ−ジングコリメ−タ
JPS6034018A (ja) * 1983-08-06 1985-02-21 Canon Inc Ｘ線コリメ−タと露光装置
JPH03120500A (ja) * 1989-10-04 1991-05-22 Toshiba Corp 多孔コリメータ及びその製造方法
US4951305A (en) * 1989-05-30 1990-08-21 Eastman Kodak Company X-ray grid for medical radiography and method of making and using same
JPH04116491A (ja) * 1990-09-07 1992-04-16 Toshiba Corp シンチレータ用コリメータ
JPH04130874A (ja) * 1990-09-21 1992-05-01 Toshiba Corp Ｘ線撮影装置
FI85775C (fi) * 1990-11-22 1992-05-25 Planmed Oy Foerfarande och anordning vid roentgenteknik.
JPH04297899A (ja) * 1991-03-27 1992-10-21 Toshiba Corp コリメータ製造方法及び該製造方法で得るコリメータ
DE4305475C1 (de) * 1993-02-23 1994-09-01 Siemens Ag Streustrahlenraster eines Röntgendiagnostikgerätes
JPH09129857A (ja) * 1995-10-27 1997-05-16 Toshiba Medical Eng Co Ltd ２次元ｘ線検出器
JP3730319B2 (ja) * 1996-06-21 2006-01-05 株式会社東芝 Ｘ線コンピュータ断層撮影装置
US5721761A (en) * 1996-09-20 1998-02-24 Ferlic; Daniel J. Radiographic grid with reduced lamellae density artifacts
US6055296A (en) * 1996-09-20 2000-04-25 Ferlic; Daniel J. Radiographic grid with reduced lamellae density artifacts
US5949850A (en) * 1997-06-19 1999-09-07 Creatv Microtech, Inc. Method and apparatus for making large area two-dimensional grids
JPH1184014A (ja) * 1997-09-05 1999-03-26 Shimadzu Corp ２次元アレイ型放射線検出器

Also Published As

Publication number Publication date
JP2001137234A (ja) 2001-05-22
US6363136B1 (en) 2002-03-26
DE50015401D1 (de) 2008-11-27
DE19947537A1 (de) 2001-04-05
EP1089297A3 (de) 2004-02-04
EP1089297A2 (de) 2001-04-04

Similar Documents

Publication Publication Date Title
EP1089297B1 (de) Gitter zur Absorption von Röntgenstrahlung
EP1107260B1 (de) Gitter zur Absorption von Röntgenstrahlen
DE102005044650B4 (de) Streustahlenraster mit einer zellenartigen Struktur von Strahlungskanälen und Verfahren zur Herstellung eines solchen Streustrahlenrasters
DE3586996T2 (de) Verfahren und geraet zu roentgenstrahlenuntersuchung.
EP1803398B1 (de) Fokus-Detektor-Anordnung zur Erzeugung von Phasenkontrast-Röntgenaufnahmen und Verfahren hierzu
DE102006063048B3 (de) Fokus/Detektor-System einer Röntgenapparatur zur Erzeugung von Phasenkontrastaufnahmen
DE112005001757B4 (de) Röntgeneinrichtung mit einem Einzelblatt-Röntgenkollimator
DE602004012080T2 (de) Nachweis von ionisierender strahlung auf dual-energie-scanning-basis
DE10136946A1 (de) Streustrahlenraster für eine Röntgeneinrichtung
DE102006017290A1 (de) Fokus/Detektor-System einer Röntgenapparatur zur Erzeugung von Phasenkontrastaufnahmen
DE102006015358A1 (de) Fokus/Detektor-System einer Röntgenapparatur zur Erzeugung von Phasenkontrastaufnahmen
DE10358866A1 (de) Gegossene Kollimatoren für CT Detektoren und Verfahren zu ihre Herstellung
DE10151562B4 (de) Anordnung aus Röntgen- oder Gammadetektor und Streustrahlenraster oder Kollimator
EP1580765B1 (de) Sekundärkollimator für eine Röntgenstreuvorrichtung sowie Röntgenstreuvorrichtung
DE102006015355A1 (de) Fokus/Detektor-System einer Röntgenapparatur zur Erzeugung von Phasenkontrastaufnahmen
EP1177767B1 (de) Computertomograph mit kegelförmigem Strahlenbündel und helixförmiger Relativbewegung
DE102005050487A1 (de) Streustrahlenraster mit mehrfachen Öffnungsabmessungen
DE3619027A1 (de) Roentgenanordnung
DE8621546U1 (de) Röntgendetektorsystem
DE2548531C2 (ja)
EP3217408B1 (de) Fokussierungsmodul für einen formfilter und formfilter zum einstellen einer räumlichen intensitätsverteilung eines röntgenstrahls
DE3881892T2 (de) Einrichtung zur schlitzradiographie.
DE3135421A1 (de) Roentgenuntersuchungsgeraet
EP0217226B1 (de) Kollimator für Strahlendiagnostikgeräte
WO2015062940A1 (de) Bildgebendes system und verfahren zur bildgebung

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

AK Designated contracting states

Kind code of ref document: A2

Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LI LU MC NL PT SE

AX Request for extension of the european patent

Free format text: AL;LT;LV;MK;RO;SI

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: KONINKLIJKE PHILIPS ELECTRONICS N.V.

Owner name: PHILIPS CORPORATE INTELLECTUAL PROPERTY GMBH

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: PHILIPS INTELLECTUAL PROPERTY & STANDARDS GMBH

Owner name: KONINKLIJKE PHILIPS ELECTRONICS N.V.

PUAL Search report despatched

Free format text: ORIGINAL CODE: 0009013

AK Designated contracting states

Kind code of ref document: A3

Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LI LU MC NL PT SE

AX Request for extension of the european patent

Extension state: AL LT LV MK RO SI

17P Request for examination filed

Effective date: 20040804

AKX Designation fees paid

Designated state(s): DE FR GB

17Q First examination report despatched

Effective date: 20070518

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): DE FR GB

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

Free format text: NOT ENGLISH

REF Corresponds to:

Ref document number: 50015401

Country of ref document: DE

Date of ref document: 20081127

Kind code of ref document: P

PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

26N No opposition filed

Effective date: 20090716

REG Reference to a national code

Ref country code: FR

Ref legal event code: ST

Effective date: 20100531

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: FR

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20090930

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 20100930

Year of fee payment: 11

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 20101129

Year of fee payment: 11

GBPC Gb: european patent ceased through non-payment of renewal fee

Effective date: 20110926

REG Reference to a national code

Ref country code: DE

Ref legal event code: R119

Ref document number: 50015401

Country of ref document: DE

Effective date: 20120403

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20120403

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: GB

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20110926