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
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
  • G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
  • G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
  • G01N23/046—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material using tomography, e.g. computed tomography [CT]
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N2223/00—Investigating materials by wave or particle radiation
  • G01N2223/40—Imaging
  • G01N2223/419—Imaging computed tomograph

Definitions

• the present invention relates to a tomographic energy dispersive diffraction imaging system (TEDDI).
• TDDI tomographic energy dispersive diffraction imaging system
• TEDDI is a relatively recently developed tomographic imaging system. Whereas most traditional tomographic imaging systems rely on absorptive or spectroscopic responses of a material object to invading radiation, TEDDI is unique in providing diffraction data in combination with either absorption or spectroscopic data. The user has the option of which parameter to display. For instance, pathological soft tissue specimens would be expected to show a small contrast in absorption whereas diffraction patterns will be significantly different between healthy and diseased tissue. The diffraction pattern across a friction stir weld for example will show the alloying composition and the absorption contrast will show macroscopic physical defects. As a further example, a ceramic material with a non-uniform spacial doping could be expected to show a variation in the fluorescence of the dopant across the sample but the absorption contrast map will yield little useful information.
• TEDDI is thus a powerful tomographic imaging system and its development has continued over recent years, see for instance Hall et al, "Synchrotron Energy- Dispersive X-ray Diffraction Tomography", Nuclear Instruments and Methods in Physics Research Section B-Beam Interactions with Materials and Atoms, 140 (1-2): 253-257 April 1998, Barnes et al, “Time and Space-resolved Dynamic Studies on Ceramic and cementation Materials", Journal of Synchrotron Radiation 7:167-177 part 3, May 2000, and Hall et al, "Non-destructive Tomographic Energy-dispersive Diffraction Imaging of the Interior of Bulk Concrete", Cement and Concrete research 30(3):491-495 March 2000.
• a white beam from a synchrotron or laboratory X-ray source collimated to the desired spacial resolution (typically with a cross section of approximately 50 ⁇ m 2 ) is directed at a sample.
• An energy resolving detector (typically a cryogenically cooled germanium solid state detector) with associated collimator is positioned to detect X-rays diffracted at an angle appropriate to the sample under investigation and the desired structural resolution.
• the track of the incident X-ray beam through the sample and the angle subtended by the detector collimator aperture defines the diffracting sample volume, referred to as the diffracting "lozenge".
• TEDDI systems developed to date is that the process of assembling a 3-D image (or even a 2-D image) is an extremely slow process commonly taking 14 to 16 hours even using synchrotron radiation. This makes existing TEDDI systems impractical for a laboratory based analytical tool and unsuitable for medical in- vivo applications.
• a tomographic energy dispersive diffraction imaging apparatus comprising: a support for a sample; a radiation source for directing incident radiation at a sample mounted on the support; detection means mounted for detecting radiation transmitted through the sample at a given angle to the direction of incidence of the radiation; the detection means comprising: an array of energy dispersive detectors and an array of collimators, such that each energy dispersive detector has a respective collimator associated therewith.
• Using a detector/collimator array in accordance with the present invention can significantly reduce the time required to obtain an image of a sample by providing information on a plurality of sample lozenges simultaneously.
• a collimator for collimating incident radiation into a collimated beam comprising at least two spaced collimator plates or foils each provided with a collimator aperture, the collimator apertures of adjacent collimator plates or foils being aligned in the direction of the collimated beam such that incident radiation passing successively through aligned apertures of adjacent collimator plates or foils is thereby collimated.
• the collimator structure according to the present invention can readily provide a densely packed array of adjacent collimators, achieving high angular resolution, ideal for use in the improved TEDDI system.
• the invention also provides a method of constructing the inventive collimator wherein the collimator apertures are formed by laser drilling.
• Figure 1 is a schematic illustration of a known TEDDI system
• FIGS. 2a - 2c schematically illustrate embodiments of part of a TEDDI system in accordance with the present invention
• Figure 3 is a schematic illustration of a known collimator structure
• Figure 4 is a schematic illustration of a collimator in accordance with the present invention.
• Figure 5 is a schematic illustration of a collimator array in accordance with the present invention.
• Figure 6 is a schematic illustration of a modification of the collimator array of Figure 5 to avoid cross-talk between adjacent collimators;
• Figure 7 is a schematic illustration of a further collimator array in accordance with the present invention.
• FIGS 8a to 8e illustrate one method of constructing a collimator in accordance with the present invention.
• FIG. 1 is a schematic illustration of a known TEDDI system.
• a white X-ray beam 1 which may for example be produced by a synchrotron or an X-ray tube is collimated by collimator 2 to produce a beam 3 of the desired spacial resolution, h a typical system the beam will have a cross section of 50 ⁇ m 2 .
• the collimated beam 3 is directed at a sample 4 which is mounted on a support (not shown) capable of scanning the sample in 3 orthogonal directions (x, y and z directions) in appropriately small steps, typically of the order of 50 ⁇ m.
• a deflected beam collimator 5 and energy dispersive detector 6 is positioned at an angle 2 ⁇ to the incident beam 3 (the angle is selected a appropriate to the sample under consideration and the desired structural resolution by application of Bragg' s Law in a known way).
• the diffracting sample volume is the lozenge 7 defined by the track of the incident beam 3 and the diffracted beam 8 accepted by the collimator 5. The size of the lozenge determines the spacial resolution.
• cryogenically cooled solid-state germanium detectors are used.
• Conventional cryogenically cooled solid-state germanium detectors are bulky items, typically around 0.5 metres in diameter, and are very expensive costing of the order of £15,000 each.
• the present inventors have recognised that a silicon pixel detector chip recently developed at the CCLRC Rutherford Appleton laboratory in Oxfordshire UK provides sufficient energy resolution in a small and relatively cheap package.
• the detector chip is described in the paper "Two Approaches To Hybrid X-ray Pixel Array Read Out", P.Seller, et.al.,SPIE Vol. 3774, Detectors for Crystallography and Diffraction Studies as Synchrotron Sources, July 1999 and consists of a 16 x 16 array of 300 ⁇ m 2 pixels each effectively constituting a discrete detector having an energy resolution of the order of 250eV at 5.9keV. This is comparable with the best quality cooled germanium detectors which have a resolution between 120eV and 180eV at 5.9keV.
• the silicon detector count rates are of the order of 1 MHz which is adequate for tomographic studies.
• Figure 1 illustrates the conventional single detector 6 and collimator 5 measuring data from a single diffraction lozenge 7 at a time.
• Figure 2a illustrates that by arranging a plurality, in this case four, detectors 9 vertically, together with their respective collimators 10, data maybe collected from four diffraction lozenges 7 simultaneously, h this case the lozenges are neighbouring along the x direction (equivalent to a corresponding x direction scan in a conventional system).
• Figure 2b illustrates that by arranging an array of detectors 9 and collimators 10 horizontally (in the Y direction) , and providing the incident beam as a vertically thin fan shape, data from neighbouring diffraction lozenges 7 in the Y direction may be collected simultaneously (equivalent to a corresponding y-direction scan in a conventional system).
• Figure 2c illustrates the effect of providing a two dimensional array of detectors 9 and collimators 10 (again with a thin fan shaped incident beam) which provides simultaneous data from a two dimensional array of diffraction lozenges, in this case lying in the x-y plane.
• Figure 3 schematically illustrates the angle of resolution of a simple collimator structure comprising a bore 11 through an otherwise solid block of absorbent material 12.
• the scale is exaggerated for clarity.
• an equivalent aspect ratio is achieved by providing apertures 15 and 16 of diameter d in respective thin plates or foils 17 and 18 of absorbent material which are spaced by the required distance L (measured between the front face of front collimator foil 17 and the back face of back collimator foil 18).
• Each collimator foil 17, 18 has a respective angular resolution ⁇ determined by the aperture diameter d and the thickness t of the foil.
• the collimator apertures could be formed by any suitable process, but in accordance with the present invention are preferably formed by laser drilling. As mentioned above, modern laser drilling can achieve an aspect ratio of 10:1 which equates, for example, to drilling a 50 ⁇ m hole in a .5mm thick foil. A practical limit of current laser drilling technology would be of the order of lO ⁇ m holes in a lOO ⁇ m thick plate and thus to achieve smaller collimator aperture sizes other technologies, such as lithographic techniques, would be required
• the collimator foils could be of any suitable material and thickness.
• the foils are preferably tungsten, which is highly absorbent to high energy X-rays, and of a self supporting thickness, e.g. of the order of 0.5mm.
• FIG. 5 schematically illustrates part of a collimator array constructed in accordance with the principals explained above in relation to Figure 4. h Figure 5 two adjacent collimators are shown (again not to scale for clarity) each comprising first and second collimator apertures 15a/16a and 15b/16b formed in front and back collimator foils 19 and 20.
• Figure 6 schematically illustrates the maximum foil separation FS between two adjacent collimator foils 21 and 22 which can be tolerated without crosstalk between adjacent collimators comprising collimator apertures 15a /16a and 15b/16b respectively.
• the maximum separation FS is related to the angular resolution ⁇ of the front foil as follows:
• each collimator foil has a thickness t of 0.5mm
• each collimator aperture has a diameter d of 50 ⁇ m
• the collimator aperture spacing s is 50 ⁇ m (i.e. collimator apertures centres are spaced by lOO ⁇ m)
• the maximum collimator foil separation avoiding cross-talk FS will be 0.5mm.
• the effective collimator length L With a foil separation FS of 0.5mm the effective collimator length L will be 1.5mm. Accordingly, applying expression (1) the angular resolution of each collimator in the array will be 0.38°. It may well be that this resolution is sufficient for some applications, but for the present application in which the required angular resolution would typically be of the order of 0.02° further collimator foils must be added until the overall collimator length L is sufficient to give the required aspect ratio L:d (in this case of the order of 6000:1).
• the overall angular resolution of the three collimator foils is related to the distance between the front face of the front collimator foil 21 and the back face of the third collimator foil 23.
• collimator foils can be added as necessary until the overall collimator length is at least equal to the required distance L.
• the number of collimator foils required is minimised by allowing the maximum separation FS between adjacent collimator foils without cross-talk.
• more than the minimum number of collimator foils may be used if desired.
• a simple construction method is illustrated schematically in Figure 8a to 8e.
• a first collimator foil 24 is mounted on an optical bench 25 (which may be of a conventional structure) and an aperture of required diameter d is drilled using a laser 26.
• the collimator aperture may have an aspect ratio 10:1 so that for instance a 50 ⁇ m diameter aperture could be drilled in a 0.5mm thick foil or a lO ⁇ m diameter aperture could be drilled in a lOO ⁇ m thick foil.
• a second collimator foil is then placed on the optical bench between the laser and the first collimator foil as illustrated in Figure 8b.
• a collimator aperture is then drilled in the second foil.
• the laser both operates to drill the required apertures and ensure that apertures of successive collimator foils are accurately aligned.
• the process may then be repeated adding additional collimator foils as indicated in Figures 8c to 8e until the required overall collimator aspect ratio is achieved.
• each collimator foil could be removed from the optical bench after being drilled allowing the next collimator foil to be positioned at the same location as the preceding collimator foil for the drilling operation so that it is located at the laser focus. Once all collimator foils have been drilled they can then be re-mounted on the optical bench and accurately positioned with the required separation.
• the laser can be used to drill an array of neighbouring collimator apertures in each of the collimator foils, in either a linear or two-dimensional array, so that the overall collimator structure comprises a similar array of individual collimators.
• the maximum spacing of adjacent collimator plates is calculated as mentioned above to ensure there is no cross-talk between adjacent collimators.
• collimator suitable for use with the detector chip technology mentioned above can readily be constructed for application in the improved TEDDI system of the present invention. It will, however, be appreciated that collimators according to the present inventions may have applications in other measurement systems.

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• 2003
  • 2003-05-31 GB GBGB0312499.7A patent/GB0312499D0/en not_active Ceased
  • 2003-12-04 US US10/558,699 patent/US7564947B2/en not_active Expired - Fee Related
  • 2003-12-04 JP JP2005500165A patent/JP4554512B2/ja not_active Expired - Fee Related
  • 2003-12-04 WO PCT/GB2003/005281 patent/WO2004106906A1/en not_active Ceased
  • 2003-12-04 EP EP03782591A patent/EP1629267A1/en not_active Ceased
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