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WO2000026922A1 - Grille antirayonnement diffuse pour detecteur a elements de detection discrets - Google Patents

Grille antirayonnement diffuse pour detecteur a elements de detection discrets Download PDF

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Publication number
WO2000026922A1
WO2000026922A1 PCT/US1999/024697 US9924697W WO0026922A1 WO 2000026922 A1 WO2000026922 A1 WO 2000026922A1 US 9924697 W US9924697 W US 9924697W WO 0026922 A1 WO0026922 A1 WO 0026922A1
Authority
WO
WIPO (PCT)
Prior art keywords
prototile
radiation
grid
width
sensitive area
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.)
Ceased
Application number
PCT/US1999/024697
Other languages
English (en)
Inventor
James E. Davis
Denny L. Y. Lee
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.)
Direct Radiography Corp
Original Assignee
Direct Radiography Corp
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 Direct Radiography Corp filed Critical Direct Radiography Corp
Priority to CA002346652A priority Critical patent/CA2346652A1/fr
Priority to EP99971575A priority patent/EP1125305A1/fr
Priority to KR1020017005337A priority patent/KR20010089373A/ko
Priority to JP2000580217A priority patent/JP2002529712A/ja
Publication of WO2000026922A1 publication Critical patent/WO2000026922A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

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
    • 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
    • G21K1/10—Scattering devices; Absorbing devices; Ionising radiation filters

Definitions

  • This invention relates to a radiation shielding grid for use with a radiation detector l o comprising a plurality of spaced discreet radiation sensing elements, and more particularly to a method for designing such grid to eliminate Moire patterns and to the resulting grid.
  • Direct radiographic imaging using panels comprising a two dimensional array of minute sensors to capture a radiation generated image is well known in the art.
  • the radiation is imagewise modulated as it passes through an object having varying radiation absorption areas.
  • Information representing an image is captured as a charge distribution stored in a plurality of charge storage capacitors in individual sensors arrayed in a two dimensional 0 matrix.
  • X-ray images are decreased in contrast by X-rays scattered from objects being imaged.
  • Anti-scatter grids have long been used (Gustov Bucky, US patent number 1,164,987 issued 1915) to absorb the scattered X-rays while passing the primary X-rays. Whenever the X-ray 5 detector resolution is comparable or higher than the spacing of the grid, an image artifact from the grid may be seen. Bucky also taught moving the anti-scatter grid to eliminate that image artifact by blurring the image of the anti-scatter grid (but not of the object, of course). The anti-scatter grid may be linear or crossed. Bucky furthermore taught a focused anti-scatter grid.
  • the sensors are positioned in the array so that there is no dead space between sensor elements.
  • the grid pitch is made equal to an integer fraction of the sensor pitch, the distance between adjacent sensor centers.
  • the grid pitch is made to correspond to the sensor pitch and is held in a steady positional relation to the detector such that the grid elements are substantially centered over the interstitial spaces.
  • a problem with the above proposed solutions is that it is difficult to construct a radiation detector having no interstitial spaces between adjacent sensor elements. When there are interstitial spaces present, maintaining the anti-scatter grid in a fixed position relative to the radiation detector array is often impractical.
  • the sensitive area with its associated interstitial space is capable of covering a entire panel surface completely without gaps and without overlaps when repeated in the horizontal and vertical directions
  • Moire patterns are reduced or completely prevented through the use of a scattered radiation shielding grid with such array of radiation sensors, wherein each sensor of the array comprises a radiation sensitive area having a width and a length, and wherein each sensitive area is separated from an adjacent sensitive area through an interstitial space.
  • the grid structure comprises a radiation absorbing material, in the form of a pattern corresponding to the combined motifs of a plurality of tiled prototiles.
  • Each prototile has a width, a length and includes a motif solely within the prototile.
  • the prototile width is equal to the radiation sensitive area width divided by a first integer.
  • the sensitive area pitch is irrelevant and instead it is the dimensions of the sensitive area (as defined below) that are used in developing the grid prototile.
  • the Moire pattern artifacts are greatly reduced or completely eliminated.
  • the aforementioned grid is created by a process comprising: a) determining a sensor width corresponding to the width of the radiation sensitive area of the sensor
  • Figure 1 shows a typical radiation detection panel comprising an array of radiation detection sensors.
  • Figure 2 shows a cross section of the panel of figure 1 along line 2-2, showing in schematic elevation one such array sensor.
  • Figure 3 shows an anti-scatter grid placed over a detection panel, the grid designed using a prototile according to one embodiment of this invention.
  • Figure 3A shows the prototile used in designing the grid of figure 3.
  • Figure 4 shows another grid designed from the assembly of a plurality of prototypes according to this invention.
  • Figure 4A shows the prototile used in designing the grid of figure 4.
  • Figure 5 shows a grid designed according to yet another embodiment of this invention.
  • Figure 5A shows the prototile used in designing the grid of figure 5.
  • Figure 6 shows a grid designed according to yet another embodiment of this invention.
  • Figure 6A shows the prototile used in designing the grid of figure 6.
  • Figure 7 shows a grid designed according to yet another embodiment of this invention.
  • Figure 7A shows the prototile used in designing the grid of figure 7.
  • Figure 8 shows a grid designed according to yet another embodiment of this invention.
  • Figure 8A shows the prototile used in designing the grid of figure 8.
  • Figure 9 shows a grid designed according to yet another embodiment of this invention.
  • Figure 9A shows the prototile used in designing the grid of figure 9.
  • Figure 10 shows a grid designed according to yet another embodiment of this invention.
  • Figure 10A shows the prototile used in designing the grid of figure 10.
  • FIG. 1 there is shown a radiation detection panel 10 useful for radiographic imaging applications.
  • the panel 10 comprises a plurality of sensors 12 arrayed in a regular pattern.
  • Each sensor comprises a switching transistor 14 and a radiation detection electrode 16 which defines the sensor radiation detection area.
  • Each radiation detection area has a width "Ws" and a length "Ls”, and is separated from an adjacent radiation detection area by an interstitial space "S". The interstitial spaces are substantially incapable of detecting incident radiation.
  • Figure 2 shows a schematic section elevation of a portion of the panel 10 viewed along arrows 2-2 in figure 1.
  • the sensor used for illustrating this invention is of the type described in United States patent Number 5,319,206 issued to Lee et al. and assigned to the assignee of this application, and in pending application serial number 08/987,485, Lee et al., filed December 9, 1997, also assigned to the assignee of this application.
  • a sensor of this type comprises a dielectric supporting base 20. On this base 20 there is constructed a switching transistor 22, usually an FET built using thin film technology.
  • the FET includes a semiconductor material 25, a gate 24, a source 26 and a drain 28. Adjacent the FET there is built a first electrode 30.
  • a dielectric layer 32 is placed over the FET and the first electrode 30.
  • a collector electrode 34 is next placed over the first electrode 30 and the FET 22.
  • an barrier or insulating layer 36 and over the insulating layer 36 a radiation detection layer 38 which is preferably a layer of amorphous Selenium.
  • a second dielectric layer 40 is deposited over the radiation detection layer, and a top electrode 42 is deposited over the top dielectric layer.
  • the barrier or insulating layer 36, the radiation detection layer 38, the second dielectric layer 40 and the top electrode layers are continuous layers extending over all the FETs and collector electrodes.
  • a static field is applied to the sensors by the application of a DC voltage between the top electrode and the first electrodes.
  • a DC voltage between the top electrode and the first electrodes.
  • electrons and holes are created in the radiation detection layer which travel under the influence of the static field toward the top electrode and the collector electrodes.
  • Each collector electrode collects charges from the area directly above it, as well as some fringe charges outside the direct electrode area.
  • There is thus an effective radiation sensitive area "W" associated with this type of sensor which is somewhat larger that the physical area of the collector electrode.
  • the sensitive areas are separated by a dead space D. In the case where the effective sensitive area is equal to the electrode area, D becomes the interstitial S space.
  • the radiation sensitive area will be the same as the physical area of the collector electrode. This is particularly true in the type of sensor which employs a photodiode together with a radiation conversion phosphor layer. In such cases the phosphor layer is usually structured as discreet columns rising above the photodiode.
  • the term "radiation sensitive area” to designate the actual area which is radiation sensitive, whether it is the same as the physical area of the sensor or not.
  • prototile width and prototile length refer to the width and length of a prototile such that its projected image on the sensitive surface satisfies the required relationships between prototile dimensions and sensitive surface dimensions, when the prototile is in the grid plane. For design purposes, this can be any plane through the grid, parallel to the width and length of the grid.
  • this plane is the plane closest to the sensitive surface.
  • the grid is usually described as having a height perpendicular to its width and length, it is to be understood that this height can also be inclined with respect to the perpendicular to produce a grid having opaque elements aligned with the incident radiation path which may be a path that diverges radially from the radiation source.
  • This type of grid element orientation is also well known in the art and grids having such inclined wall are described in the aforementioned US patent 4,951,305 Moore et al. (See particularly Moore, figure 8.) Grids having such oriented elements are still to considered as being included when there is reference to a grid height.
  • the projected and actual dimensions will be substantially the same, in which case the actual dimensions will be convenient to use.
  • Figure 3 shows a radiation detection panel of the type described above with a scattered radiation shielding grid 44 placed over the panel.
  • the grid comprises a plurality of opaque strips 46 and 48 aligned along the width and length of the panel.
  • This type of anti-scatter grid is a common type of anti-scatter grid available, and may be manufactured easily. See for instance US patent number 5,606,589 issued to Pellegrino et al. which discloses such a cross grid and a method for its manufacture and use in medical radiography.
  • grid 44 is not aligned with the interstitial or dead spaces of the underlying array of sensitive areas 11. Unlike the Tsukamoto grid, grid 44 may be placed anywhere and still function effectively. Further more the grid may be moved during the radiation exposure.
  • Grid 44 has been designed in accordance with this invention by tiling a plurality of prototiles 50 shown in dotted lines in figure 3.
  • Tiling in the present context means the assembly of a plurality of prototiles by arraying the prototiles contiguously side by side to form a large area comprising a plurality of prototiles.
  • the prototile 50 has a width Wp and a length Lp.
  • the width of the prototile Wp equals the width Ws of the radiation sensitive area 11 of the sensor of the panel divided by an integer A.
  • Each of the prototiles includes a motif 52 which will be used to design the opaque portion of the grid.
  • this motif is a cross.
  • the motif is selected such that when the prototiles are tiled, the motifs of the plurality of the tiled prototiles combined form the pattern shown in figure 3. This is the pattern for the opaque material in the grid.
  • the grid pattern need not be a plurality of strips intersecting at 90° angles.
  • a number of different grid designs can be produced using the technology disclosed in US patent number 5,259,016 issued to Dickerson et al.
  • the use photographic techniques to produce radiation absorption grids having shapes other than straight lines is shown in that reference and can be used to produce grids designed using the present invention wherein the opaque grid strips are other than straight lines.
  • the aforementioned US 4,951,305 issued to Moore et al. also teaches methods for producing complex grid shapes.
  • Figure 4 shows a grid 44 generated from a prototile 50 having a width Wp and a length Lp and motif 54 shown as a single bar.
  • the radiation sensitive area 11 has a width Ws, a length Ls.
  • the interstitial space S separates the sensitive areas.
  • the resultant anti-scatter grid 44 is in many respects like the common linear anti-scatter grid in common use today, except the distance between the opaque regions is equal to the sensitive area width of the sensor. For a sensitive area having a width of 135 microns the grid 44 would preferably have 188.1 bars per inch (7.407 per mm).
  • the grid has a third dimension along the z axis, or in other words the grid walls have a height.
  • the wall height ranges from about 2 to 16 times the thickness of the wall.
  • a preferred height ratio is about 6 to 12.
  • the ratio of wall thickness to the prototype width ranges from about 1/10 to Vi with a preferred ratio of about 1/6.
  • the projection of the grid on the panel will be both magnified and distorted depending on the distance of the grid from the radiation sensitive surface, and to some extent depending on the distance and nature of the radiation source.
  • a collimated radiation source for instance, will produce no magnification or distortion effect, while a point source will produce both.
  • These effects are well understood in the art and proper compensation to the grid design will be made, by designing a grid such that the projected prototile on the panel will satisfy the above developed criteria. These effects are minimized by placing the grid in close proximity and preferably intimate contact with the sensitive area, and by minimizing the grid wall height.
  • the preferred grid 44 would have 190.0 pairs per inch (7.480 per mm) to correct for the geometric magnification, instead of 188.1 bars per inch (7.407 per mm).
  • the radiation sensitive areas 11 of the radiation detector panel need not be in a regular array. As shown in figure 5, they may be unevenly arrayed and still enjoy the benefits of this invention. However, the radiation sensitive areas must be identical in shape, size and orientation.
  • Figure 5 and its associated prototile shown in figure 5A also illustrate a grid design and prototile motif 56 for the case where the radiation sensitive area width is different from the sensitive area length. As shown the resulting prototile width and length are also different.
  • a preferred X-ray transparent region will have no edges collinear with either edge of the sensitive area as shown in the grid of figure 5.
  • Preferred X-ray opaque motifs may include circles, ovals, rectangles, and other shapes. The intention is to minimize the amount of the opaque motif of the prototile projected on the sensitive area boundary as the motif shifts its relative position with respect to the sensitive area along the panel surface. Because the resulting opaque pattern following tiling has a pitch that is less than the sensor pitch, invariably the opaque pattern will fall on the line that divides the sensitive area from the interstitial area (See figure 4).
  • Figures 6A and 7A show alternate motifs M resulting in grid 44 structures shown in figures 6 and 7 which do not include opaque areas parallel to the aforementioned boundary.
  • Figures 8, 9, and 10 all show different grids 44 designed according to the present invention.
  • the prototiles 50 and motifs M used in these cases are shown in figures 8A, 9A, and 10A respectively.
  • the prototile 50 has a width Wp and a length Lp as defined hereinabove.
  • the resulting grid of radiation absorbing pattern is such that the radiation opaque area of the grid always covers the same amount of radiation sensitive area in each sensor, regardless of the position of the grid.
  • a grid will be constructed as follows. First, the effective radiation detection area of the panel sensors is determined to identify the radiation sensitive area and the prototile size is then determined according to the relationships given above. Next, a desired motif is created in the prototile. The prototile is then duplicated and a plurality of prototiles assembled to create the pattern of the grid which results from the combined motifs of the prototiles. Mirror images of the prototile may be used with the original prototile to create a pattern. This pattern is then used for the radiation absorption material which forms the anti-scatter grid. This material may be lead.
  • the grid may be constructed according to the teachings of the aforementioned US patents to Dickerson et al., Pellegrino et al. or Moore et al. If the grid is not to be in contact with the detectors and the radiation source is a point source, the prototile design takes into account the projection of the grid onto the sensitive area.

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  • 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)
  • Solid State Image Pick-Up Elements (AREA)
  • Image Input (AREA)
  • Transforming Light Signals Into Electric Signals (AREA)

Abstract

L'invention concerne une grille de protection (44) constituée d'un matériau absorbant le rayonnement (46, 48) destiné à être utilisé avec un réseau de capteurs de rayonnement non contigus discrets afin de protéger ces capteurs du rayonnement diffusé. Les capteurs présentent chacun une surface (11) sensible au rayonnement ayant une largeur (Ws) et une longueur (Wl). Dans la conception de la grille on a développé un pavé primitif ayant une largeur et une longueur de pavé primitif. La largeur du pavé primitif est égale à la largeur de la surface sensible au rayonnement divisée par un nombre entier, et la longueur du pavé primitif est aussi égale à la longueur de la surface sensible aux rayonnements divisée par un nombre entier. Le pavé primitif contient un dessin contenu uniquement à l'intérieur du pavé primitif formant un motif lorsqu'une pluralité de pavés primitifs suffisants pour recouvrir le réseau de détecteurs discrets sont agencés de façon contiguë. La grille est construite avec le matériau absorbant le rayonnement dans ce motif.
PCT/US1999/024697 1998-10-29 1999-10-21 Grille antirayonnement diffuse pour detecteur a elements de detection discrets Ceased WO2000026922A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
CA002346652A CA2346652A1 (fr) 1998-10-29 1999-10-21 Grille antirayonnement diffuse pour detecteur a elements de detection discrets
EP99971575A EP1125305A1 (fr) 1998-10-29 1999-10-21 Grille antirayonnement diffuse pour detecteur a elements de detection discrets
KR1020017005337A KR20010089373A (ko) 1998-10-29 1999-10-21 정밀한 검출소자가 구비된 검출기용 확산방지 방사선 그리드
JP2000580217A JP2002529712A (ja) 1998-10-29 1999-10-21 検出素子を有した検出器用散乱防止放射線グリッド

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US18170398A 1998-10-29 1998-10-29
US09/181,703 1998-10-29

Publications (1)

Publication Number Publication Date
WO2000026922A1 true WO2000026922A1 (fr) 2000-05-11

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PCT/US1999/024697 Ceased WO2000026922A1 (fr) 1998-10-29 1999-10-21 Grille antirayonnement diffuse pour detecteur a elements de detection discrets

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EP (1) EP1125305A1 (fr)
JP (1) JP2002529712A (fr)
KR (1) KR20010089373A (fr)
CA (1) CA2346652A1 (fr)
WO (1) WO2000026922A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004510992A (ja) * 2000-10-04 2004-04-08 ダイレクト　ラジオグラフィー　コーポレーション 離散的検知要素を具備する検知器用の散乱防止放射線グリッド
DE10151562B4 (de) * 2001-10-23 2004-07-22 Siemens Ag Anordnung aus Röntgen- oder Gammadetektor und Streustrahlenraster oder Kollimator
EP1639945A1 (fr) * 2004-09-24 2006-03-29 Hitachi, Ltd. Dispositif pour formation d'image de rayonnement et appareil de diagnostic de medicine nucleaire utilisant cet dispositif

Families Citing this family (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3848107B2 (ja) * 2001-07-24 2006-11-22 キヤノン株式会社 放射線画像撮影装置
JP3793139B2 (ja) * 2002-10-25 2006-07-05 キヤノン株式会社 Ｘ線撮像装置
KR100907925B1 (ko) * 2007-04-20 2009-07-16 정원정밀공업 주식회사 Ｘ선 촬영장치용 그리드 및 그 제조방법
JP5319331B2 (ja) * 2009-03-03 2013-10-16 株式会社東芝 放射線検出装置
JP5237919B2 (ja) * 2009-11-13 2013-07-17 株式会社日立製作所 核医学診断装置
KR101151024B1 (ko) * 2010-04-26 2012-06-13 주식회사 디알텍 그리드 장치 및 엑스선 검출장치
US20110261925A1 (en) * 2010-04-26 2011-10-27 DRTECH Corporation Grid apparatus and x-ray detecting apparatus
JP2014039569A (ja) * 2010-12-14 2014-03-06 Fujifilm Corp 放射線画像撮影用グリッド及び放射線画像撮影システム
KR101276741B1 (ko) * 2012-10-22 2013-06-19 성균관대학교산학협력단 방사성 화합물 합성장치
KR101684730B1 (ko) * 2014-02-25 2016-12-08 고려대학교 산학협력단 디지털 방사선 검출기

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5606589A (en) * 1995-05-09 1997-02-25 Thermo Trex Corporation Air cross grids for mammography and methods for their manufacture and use
US5666395A (en) * 1995-09-18 1997-09-09 Kabushiki Kaisha Toshiba X-ray diagnostic apparatus

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5606589A (en) * 1995-05-09 1997-02-25 Thermo Trex Corporation Air cross grids for mammography and methods for their manufacture and use
US5666395A (en) * 1995-09-18 1997-09-09 Kabushiki Kaisha Toshiba X-ray diagnostic apparatus

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004510992A (ja) * 2000-10-04 2004-04-08 ダイレクト　ラジオグラフィー　コーポレーション 離散的検知要素を具備する検知器用の散乱防止放射線グリッド
DE10151562B4 (de) * 2001-10-23 2004-07-22 Siemens Ag Anordnung aus Röntgen- oder Gammadetektor und Streustrahlenraster oder Kollimator
US6778632B2 (en) 2001-10-23 2004-08-17 Siemens Aktiengesellschaft X-ray detector/stray radiation grid and gamma detector/collimator arrangements
EP1639945A1 (fr) * 2004-09-24 2006-03-29 Hitachi, Ltd. Dispositif pour formation d'image de rayonnement et appareil de diagnostic de medicine nucleaire utilisant cet dispositif
US7442937B2 (en) 2004-09-24 2008-10-28 Hitachi, Ltd. Radiation imaging apparatus and nuclear medicine diagnosis apparatus using the same

Also Published As

Publication number Publication date
JP2002529712A (ja) 2002-09-10
EP1125305A1 (fr) 2001-08-22
KR20010089373A (ko) 2001-10-06
CA2346652A1 (fr) 2000-05-11

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