WO2014134634A2 - Large field of view grating interferometers for x-ray phase contrast imaging and ct at high energy - Google Patents
Large field of view grating interferometers for x-ray phase contrast imaging and ct at high energy Download PDFInfo
- Publication number
- WO2014134634A2 WO2014134634A2 PCT/US2014/033561 US2014033561W WO2014134634A2 WO 2014134634 A2 WO2014134634 A2 WO 2014134634A2 US 2014033561 W US2014033561 W US 2014033561W WO 2014134634 A2 WO2014134634 A2 WO 2014134634A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- interferometer
- gratings
- contrast
- grating
- ray
- Prior art date
Links
- 238000003384 imaging method Methods 0.000 title abstract description 35
- 239000000758 substrate Substances 0.000 claims abstract description 18
- 238000003325 tomography Methods 0.000 claims abstract description 4
- 238000000034 method Methods 0.000 abstract description 12
- 238000009659 non-destructive testing Methods 0.000 abstract description 6
- 238000012216 screening Methods 0.000 abstract description 2
- 210000000988 bone and bone Anatomy 0.000 description 12
- 210000004872 soft tissue Anatomy 0.000 description 12
- 235000012431 wafers Nutrition 0.000 description 12
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 12
- 238000001228 spectrum Methods 0.000 description 10
- 238000010521 absorption reaction Methods 0.000 description 9
- 210000003127 knee Anatomy 0.000 description 9
- 230000005540 biological transmission Effects 0.000 description 7
- 238000013461 design Methods 0.000 description 7
- 230000035945 sensitivity Effects 0.000 description 7
- 238000001514 detection method Methods 0.000 description 6
- 230000003287 optical effect Effects 0.000 description 6
- 230000007423 decrease Effects 0.000 description 5
- 239000004677 Nylon Substances 0.000 description 4
- 230000000694 effects Effects 0.000 description 4
- 210000003414 extremity Anatomy 0.000 description 4
- 238000005286 illumination Methods 0.000 description 4
- LFEUVBZXUFMACD-UHFFFAOYSA-H lead(2+);trioxido(oxo)-$l^{5}-arsane Chemical compound [Pb+2].[Pb+2].[Pb+2].[O-][As]([O-])([O-])=O.[O-][As]([O-])([O-])=O LFEUVBZXUFMACD-UHFFFAOYSA-H 0.000 description 4
- 229920001778 nylon Polymers 0.000 description 4
- 229920003229 poly(methyl methacrylate) Polymers 0.000 description 4
- 239000004926 polymethyl methacrylate Substances 0.000 description 4
- 238000002083 X-ray spectrum Methods 0.000 description 3
- 239000006096 absorbing agent Substances 0.000 description 3
- 238000011161 development Methods 0.000 description 3
- 238000002474 experimental method Methods 0.000 description 3
- 238000005305 interferometry Methods 0.000 description 3
- 238000004519 manufacturing process Methods 0.000 description 3
- 241000156978 Erebia Species 0.000 description 2
- 238000004458 analytical method Methods 0.000 description 2
- 230000008901 benefit Effects 0.000 description 2
- 229910052799 carbon Inorganic materials 0.000 description 2
- 210000000845 cartilage Anatomy 0.000 description 2
- 230000001427 coherent effect Effects 0.000 description 2
- 238000002591 computed tomography Methods 0.000 description 2
- 230000001054 cortical effect Effects 0.000 description 2
- 238000002059 diagnostic imaging Methods 0.000 description 2
- 230000036541 health Effects 0.000 description 2
- 230000006872 improvement Effects 0.000 description 2
- 210000002414 leg Anatomy 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 210000003205 muscle Anatomy 0.000 description 2
- 230000005855 radiation Effects 0.000 description 2
- 238000002601 radiography Methods 0.000 description 2
- 230000003595 spectral effect Effects 0.000 description 2
- 238000012360 testing method Methods 0.000 description 2
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- 101800004637 Communis Proteins 0.000 description 1
- 208000006735 Periostitis Diseases 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 238000002050 diffraction method Methods 0.000 description 1
- 230000009977 dual effect Effects 0.000 description 1
- IDGUHHHQCWSQLU-UHFFFAOYSA-N ethanol;hydrate Chemical compound O.CCO IDGUHHHQCWSQLU-UHFFFAOYSA-N 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 210000001145 finger joint Anatomy 0.000 description 1
- 239000012530 fluid Substances 0.000 description 1
- 230000004907 flux Effects 0.000 description 1
- 210000001564 haversian system Anatomy 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 210000000629 knee joint Anatomy 0.000 description 1
- 230000003902 lesion Effects 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 210000003460 periosteum Anatomy 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 108090000623 proteins and genes Proteins 0.000 description 1
- 102000004169 proteins and genes Human genes 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 210000002435 tendon Anatomy 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 238000002491 ultra-small angle X-ray scattering Methods 0.000 description 1
- 210000000466 volar plate Anatomy 0.000 description 1
Classifications
-
- 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]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4035—Arrangements for generating radiation specially adapted for radiation diagnosis the source being combined with a filter or grating
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/48—Diagnostic techniques
- A61B6/484—Diagnostic techniques involving phase contrast X-ray imaging
-
- 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
- G01N23/20—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 using diffraction of the radiation by the materials, e.g. for investigating crystal structure; by using scattering of the radiation by the materials, e.g. for investigating non-crystalline materials; by using reflection of the radiation by the materials
- G01N23/20008—Constructional details of analysers, e.g. characterised by X-ray source, detector or optical system; Accessories therefor; Preparing specimens therefor
-
- 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
- G01N23/20—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 using diffraction of the radiation by the materials, e.g. for investigating crystal structure; by using scattering of the radiation by the materials, e.g. for investigating non-crystalline materials; by using reflection of the radiation by the materials
- G01N23/20075—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 using diffraction of the radiation by the materials, e.g. for investigating crystal structure; by using scattering of the radiation by the materials, e.g. for investigating non-crystalline materials; by using reflection of the radiation by the materials by measuring interferences of X-rays, e.g. Borrmann effect
-
- 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
- G01N23/20—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 using diffraction of the radiation by the materials, e.g. for investigating crystal structure; by using scattering of the radiation by the materials, e.g. for investigating non-crystalline materials; by using reflection of the radiation by the materials
- G01N23/207—Diffractometry using detectors, e.g. using a probe in a central position and one or more displaceable detectors in circumferential positions
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B5/00—Optical elements other than lenses
- G02B5/18—Diffraction gratings
- G02B5/1814—Diffraction gratings structurally combined with one or more further optical elements, e.g. lenses, mirrors, prisms or other diffraction gratings
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B5/00—Optical elements other than lenses
- G02B5/18—Diffraction gratings
- G02B5/1814—Diffraction gratings structurally combined with one or more further optical elements, e.g. lenses, mirrors, prisms or other diffraction gratings
- G02B5/1819—Plural gratings positioned on the same surface, e.g. array of gratings
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B5/00—Optical elements other than lenses
- G02B5/18—Diffraction gratings
- G02B5/1866—Transmission gratings characterised by their structure, e.g. step profile, contours of substrate or grooves, pitch variations, materials
- G02B5/1871—Transmissive phase gratings
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
- G01N15/10—Investigating individual particles
- G01N15/14—Optical investigation techniques, e.g. flow cytometry
- G01N15/1434—Optical arrangements
- G01N2015/1454—Optical arrangements using phase shift or interference, e.g. for improving contrast
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/41—Refractivity; Phase-affecting properties, e.g. optical path length
- G01N2021/4173—Phase distribution
- G01N2021/4186—Phase modulation imaging
-
- 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
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B5/00—Optical elements other than lenses
- G02B5/18—Diffraction gratings
- G02B5/1838—Diffraction gratings for use with ultraviolet radiation or X-rays
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B5/00—Optical elements other than lenses
- G02B5/18—Diffraction gratings
- G02B5/1842—Gratings for image generation
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
- G02B6/02—Optical fibres with cladding with or without a coating
- G02B6/02057—Optical fibres with cladding with or without a coating comprising gratings
- G02B6/02076—Refractive index modulation gratings, e.g. Bragg gratings
- G02B6/0208—Refractive index modulation gratings, e.g. Bragg gratings characterised by their structure, wavelength response
- G02B6/02085—Refractive index modulation gratings, e.g. Bragg gratings characterised by their structure, wavelength response characterised by the grating profile, e.g. chirped, apodised, tilted, helical
-
- 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
- G21K2207/00—Particular details of imaging devices or methods using ionizing electromagnetic radiation such as X-rays or gamma rays
- G21K2207/005—Methods and devices obtaining contrast from non-absorbing interaction of the radiation with matter, e.g. phase contrast
Definitions
- the present disclosure relates generally to medical imaging. More particularly the present disclosure relates to a device to provide large field-of-view phase contrast imaging with high energy X-ray.
- a Talbot-Lau interferometer consists of three micro-period gratings: 'source', 'beam-splitter', and 'analyzer'.
- the source and analyzer are absorption grating typically made of Au, while the beam-splitter is a thin phase grating typically made of Si or Ni.
- DPC differential phase-contrast
- the interferometer must work at high energy. For instance, X-ray DPC imaging for the knee can potentially be done, for which radiography is typically done at 60-65 kVp (40-45 keV mean spectral energy) and conventional CT at 80-90 kVp (55-60 keV mean energy).
- an interferometer must be very sensitive to small X-ray angular changes to enable refraction imaging with acceptable dose.
- the sensitivity is determined by two parameters: the fringe contrast or 'visibility' V, and the angular resolution, W.
- High contrast in the >20% range approximately is essential for medical DPC imaging, because the signal-to-noise ratio (SNR) in the DPC images improves rapidly with increasing contrast (e.g., as ⁇ V 2 in DPC-CT).
- Good angular resolution W ⁇ several ⁇ -radian is also needed, because the X-ray refraction angles in soft tissue are in the sub ⁇ -radian range.
- the requirements for high contrast and angular resolution are more critical at high X-ray energy, because the refraction angles decrease with energy as ⁇ 1/E 2 .
- the Talbot-Lau interferometer For DPC imaging of large body parts the Talbot-Lau interferometer must have >20% contrast at mean spectral energies >40 keV, while using gratings with ⁇ 10 ⁇ period. This is not possible however with the conventional normal incidence Talbot-Lau interferometer, because the thickness of few micron period absorption gratings is technologically limited to -100 ⁇ .
- a device that enables phase contrast imaging at high X-ray energy is the glancing angle Talbot-Lau interferometer (GAI), in which the gratings have bars inclined at an angle ⁇ ⁇ 10 - 30° along the beam direction.
- the effect of inclining the gratings is to increase the effective absorber thickness from the normal incidence value t, to t/sin(a).
- the interferometer also has multiple tiled micro-periodic gratings arranged on the substrate.
- the gratings include absorbing bars that are tilted at a glancing angle along the direction of the incident radiation.
- the absorbing bars are aligned parallel with the incident X-rays wherein the gratings have a fixed period along a grating bar direction.
- the interferometer device is configured for use in a large FOV DPC imaging system.
- the substrate can take the form of a single Si or C wafer.
- Multiple GAI gratings can be 'tiled' on the substrate and rotated to follow the X-ray beam direction as in FIG 2, to achieve large horizontal FOV. Also, the gratings can be stacked in a vertical direction to make a large FOV in both the horizontal and vertical directions, to be used for DPC-CT or DPC radiography.
- the absorbing bars of the gratings are also inclined at an angle of approximately 10° to approximately 30° along the beam direction.
- FIG. IB illustrates grating bars for a GAI interferometer.
- FIG. 2A illustrates a tiled glancing angle grating interferometer (GAI) having multiple grating blocks oriented parallel to the incident X-rays on a single substrate, according to an embodiment of the present disclosure.
- FIG. 2B shows an example arrangement of the sub-grating that are joined together in such a manner that the grating pattern is only slightly perturbed.
- GAI glancing angle grating interferometer
- FIG. 3 illustrates Moire fringes and high fringe contrast obtained with a GAI interferometer operated in 'tiled' mode.
- FIGS. 4A-4C shows an example design for a clinical scanner for large extremity joints consistent with embodiments of the disclosure, where FIG. 4A shows a large FOV analyzer grating using three tiled wafers, FIG. 4B shows a side view of the scanner, and FIG. 4C shows a top view of the scanner.
- FIG. 5 illustrates a glancing angle Talbot-Lau interferometer using gratings with the bars inclined at an angle ⁇ ⁇ 10 - 30° along the beam direction, according to an embodiment of the present disclosure.
- FIGS. 6A and 6B illustrate a large increase in contrast at high energy with the glancing angle interferometer, according to an embodiment of the present disclosure.
- FIG. 7 illustrates the field of view vignetting that occurs in the GAI interferometer without tiling, according to an embodiment of the present disclosure.
- FIG. 8 illustrates images of a small joint phantom in water obtained with the GAI at high energy, according to an embodiment of the present disclosure.
- FIGS. 9A and 9B illustrate attenuation and DPC images of a -40 mm diameter veal bone embedded in a whole veal leg, having -120 mm thick muscle, obtained at 80 kVp energy with the GAI device, according to an embodiment of the present disclosure.
- FIG. 10 shows DPC-CT and attenuation CT images of a human finger joint, obtained with 5.4 ⁇ and with 10 ⁇ glancing angle interferometers operated at 60 and 80 kVp respectively, according to an embodiment of the present disclosure.
- the numerical values as stated for the parameter can take on negative values.
- the example value of range stated as "less that 10" can assume negative values, e.g. - 1, -2, -3, - 10, -20, -30, etc.
- a device and method of the present disclosure provides large field-of-view Talbot-Lau phase contrast CT systems up to very high X-ray energy.
- the device includes micro-periodic gratings tilted at glancing incidence and tiled on a single substrate to provide the large field-of-view needed for phase contrast CT systems.
- the present disclosure is a simple, economical, and accurate method for combining multiple GAIs into a larger FOV system, capable of performing phase-contrast tomography (DPC-CT) on large objects at high X-ray energy.
- the device and method can be applied to medical X-ray imaging, industrial non-destructive testing, and security screening.
- X-ray differential phase-contrast (DPC) or refraction based imaging with Talbot-Lau grating interferometers has the potential to become a new medical imaging modality, offering improved soft tissue contrast and spatial resolution in comparison with conventional attenuation based imaging.
- DPCCT X-ray differential phase-contrast
- refraction based imaging with Talbot-Lau grating interferometers has the potential to become a new medical imaging modality, offering improved soft tissue contrast and spatial resolution in comparison with conventional attenuation based imaging.
- DPCCT could enable the detection of small lesions in soft tissue, which is not possible with other imaging modalities.
- New bone imaging modalities may also be possible.
- the present disclosure includes use of multiple 'tiled' micro-periodic gratings having the absorbing bars tilted at a glancing angle along the direction of the incident radiation, and also aligned parallel with the incident X-rays, as illustrated in FIG. 2A.
- the tiling of the tilted gratings is an advancement over the Talbot-Lau Glancing Angle
- GAI Interferometer
- the present disclosure also includes use of multiple tiled GAI gratings on a single substrate, as also shown in FIG.2.
- the use of a single substrate strongly simplifies interferometer alignment and eliminates the need for many costly micro-positioning stages, since the 'sub-gratings' or grating blocks are pre-aligned with few nm precision through the lithographic manufacturing process.
- FIG. 2A illustrates multiple tiled glancing angle grated interferometer (GAI) gratings on a single substrate, according to an embodiment of the present disclosure.
- GAI grated interferometer
- FIG. 2A multiple 'sub-gratings' or grating blocks with slightly rotated lines are positioned on a single substrate or wafer. All the sub-gratings have equal period and width; the width is equal or less than the FWHM of their vignetting curve (e.g., approximately 10 mm for a 10 ⁇ period grating at 10° angle and having 2m length).
- the rotation angle follows the central ray direction for each sub-grating.
- a 6" Si wafer would accommodate 12 sub-gratings of 10 mm width and 90 mm height, giving a FOV at the detector of 120 mm width and 30 mm height, at a glancing angle of 20°.
- Several such wafers side by side would cover a contiguous FOV of a few tens of cm wide, sufficient for full cone-beam CT of large objects.
- FIG. 3 illustrates the Moire fringes and their contrast obtained in this setup, confirming that high interferometer contrast can be obtained with the gratings positioned far from the on-axis position.
- the tiled gratings can be further stacked in the vertical direction to make large horizontal and vertical FOV PC-CT systems, as illustrated in FIGS. 4A-4C.
- the tiled grating glancing angle interferometer offers thus a path towards the development of high energy DPC-CT systems, such as for CT of large extremity joints or head.
- FIGS. 4A-4C show example views of a cone-beam GAI-CT scanner and imager that can be used for the clinical evaluation of extremity joints consistent with implementations of the present disclosure, where FIG. 4A shows a large FOV analyzer grating using three tiled wafers and FIGS. 4B and 4C show a side view and a top view of the scanner, respectively.
- the system can work between 75-100 kVp, corresponding to transmitted spectra with 55-65 keV mean energy for the average human knee. This range encompasses that optimal for attenuation CT of extremities (80-90 kVp).
- the system uses a symmetric GAI design with gratings of equal period of about 5 ⁇ , 100 ⁇ thickness, and operated in the 3 rd Talbot order (-1.5 m length), at -12° glancing angle. Calculations have shown that the 3 rd order maximizes the product of the angular sensitivity and contrast and thus the DPC-CT SNR.
- the computed fringe contrast as a function of energy is shown in FIG. 1A (curve marked 600 ⁇ ), indicating high spectrally averaged contrast of -30%.
- FIG. 4A The design of a large area tiled grating is shown in FIG. 4A.
- a 30 cm wide by 20 mm tall FOV is achieved by overlapping three 6" wafers, carrying each a 100x100 mm tiled grating array composed of 10 sub-gratings of 10 mm width, inclined at 12°.
- the sub- gratings can be joined together in such a manner that the grating pattern is only slightly perturbed, as shown in FIG. 2B.
- the wafers can be placed on a precision machined tray with clear apertures.
- the partial overlap between the grating substrates leads to only a small increase in beam attenuation.
- the tiled grating can have the fanned geometry, as shown in FIG.
- the tiled GAI gratings are used to achieve a wide (e.g. 30 cm) FOV at the detector, while large FOV height is obtained by vertically stacking several rows of tiled GAIs.
- 'slot-scan' DPC-CT systems can be built in which the object (e.g. a knee) is helically scanned with single row of GAI gratings.
- FIGS. 4B and 4C show a side view and top view of the scanner 400, respectively.
- the scanner 400 includes a first arm 405 arranged to support the Talbot-Lau interferometer in a vibration free manner.
- the interferometer includes a source grating GO 410, a phase grating Gl 415 and an analyzer grating G2 420.
- a second arm 425, separate from the first arm 405, is arranged to support the X-ray tube 430 and the detector 435.
- the first arm 405 and/or second arm 425 can be made of light, stiff, and thermally stable carbon honeycomb, such as used in space optics instrumentation as in known in the art.
- the scanner 400 can be mounted on a large bore stepper stage (not shown in detail) which will rotate it around a sample 435.
- the X-ray tube 430 can be a dc tube instead of a pulsed one to eliminate the system or background phase variation due to pulsed X-ray heating of the source grating.
- An example of a suitable tube is the MXR-160HP/11 industrial tube made by Comet,
- This X-ray tube provides a compact, light and vibration free X-ray source that is well suited for scanning together with the sensitive interferometer.
- Other similar type X-ray source could also be used as is known in the art.
- the detector 435 can be a high efficiency, direct coupled Csl/CCD, such as the ARGUS model developed by Teledyne DALSA Inc. for panoramic imaging. This detector has about an order of magnitude higher sensitivity than a typical CMOS flat panel, and a wide form factor well suited for a slot-scan clinical system.
- the pixel size can be varied between 27-160 ⁇ and the acquisition time is > 0.125s. Other similar type detectors could also be used as is known in the art.
- the tiled GAI grating Talbot-Lau interferometer described with respect to the present disclosure can be directly applied for X-ray phase-contrast CT at high energy, without any further development.
- the design may be further optimized, particularly with respect to the sub-grating dimensions and angles, to physically demonstrate such systems, and to build prototypes for medical, security and NDT applications.
- a glancing angle Talbot-Lau interferometer using gratings with the bars inclined at an angle ⁇ ⁇ 10 - 30° along the beam direction is illustrated in FIG. 5. The effect of inclining the gratings is to increase the effective absorber thickness from the normal incidence value t, to t/sin(a).
- FIG. 1A The expected contrast improvement is illustrated in FIG. 1A with the computed contrast for the above interferometer assuming that the 100 ⁇ Au gratings are inclined at an angle a - 10° (600 ⁇ effective thickness). The contrast strongly increases at high energy, leading to about a five-fold improvement in the spectrally averaged contrast.
- the differential phase contrast X-ray imaging system 500 includes an X- ray illumination system 502, a beam splitter 104 arranged in an optical path 506 of the X-ray illumination system 502, and a detection system 508 arranged in an optical path 510 to detect X-rays after passing through the beam splitter 504.
- the detection system 108 includes an X- ray detection component 512.
- the beam splitter 504 includes a splitter grating arranged to intercept an incident X-ray beam and provide an interference pattern of X-rays.
- beam splitter 504 can be a thin phase grating made of Si or Ni.
- the detection system 508 also includes an analyzer grating 514 arranged to intercept and block at least portions of the interference pattern of X-rays prior to reaching the X-ray detection component 512.
- the analyzer grating 514 has a longitudinal dimension, a lateral dimension that is orthogonal to the longitudinal dimension, and a transverse dimension that is orthogonal to the longitudinal and lateral dimensions.
- the analyzer grating 514 has a pattern of optically dense regions, each having a longest dimension along the longitudinal dimension and spaced substantially parallel to each other in the lateral dimension such that there are optically rare regions between adjacent optically dense regions.
- Each optically dense region has a depth in the transverse dimension that is smaller than a length in the longitudinal dimension.
- the analyzer grating 514 is arranged with the longitudinal dimension at a shallow angle relative to incident X-rays such that the shallow angle is less than 30 degrees.
- the longitudinal dimension of the analyzer grating 514 is oriented substantially along the optical path 510 (which can be the optical axis, for example), except tilted at the shallow angle . (This will also be referred to as a glancing angle.)
- each optically dense region has a depth in the transverse dimension that is smaller than a length in the longitudinal dimension by at least a factor of two. In an embodiment, each optically dense region has a depth in the transverse dimension that is smaller than a length in the longitudinal dimension by at least a factor of ten. In a further embodiment, each optically dense region has a depth in the transverse dimension that is smaller than a length in the longitudinal dimension by at least a factor of one hundred.
- the shallow angle is less than 25 degrees and greater than 5 degrees. In another embodiment, the shallow angle is less than 15 degrees and greater than 3 degrees.
- An embodiment of the current disclosure is directed to medical applications. Since it is difficult to produce few-micron period gratings with more than -100 ⁇ Au absorber thickness, inclining the gratings at an angle in the 5-25° range makes for 200-1000 ⁇ effective Au thickness. As is shown in FIG. 1A, this thickness enables >90% X-ray absorption (and thus high interferometer contrast) over the -40 keV-1 10 keV energy range, of interest for medical phase-contrast imaging deep in the body. Another embodiment is directed to industrial or non-destructive testing (NDT) applications.
- NDT non-destructive testing
- the effective Au thickness is in the 400-2000 ⁇ range, which makes for good X-ray absorption and interferometer contrast in the -100 keV-250 keV energy range of interest for industrial NDT applications.
- the splitter grating 504 is a reflection grating (not shown). In an embodiment of the current invention, the splitter grating 504 is a transmission grating. According to an embodiment of the current disclosure in which the splitter grating 504 is a transmission grating, similar to analyzer grating 514, such an embodiment of the analyzer grating has a longitudinal dimension, a lateral dimension that is orthogonal to the longitudinal dimension, and a transverse dimension that is orthogonal to the longitudinal and lateral dimensions.
- the splitter grating 504 in this embodiment has a pattern of optically dense regions, each having a longest dimension along the longitudinal dimension and being spaced substantially parallel to each other in the lateral dimension such that there are optically rare regions between adjacent optically dense regions. Each optically dense region has a depth in the transverse dimension that is smaller than a length in the longitudinal dimension.
- the splitter grating 504 is arranged with the longitudinal dimension at a shallow angle relative to incident X-rays such that it is less than 30 degrees.
- the splitter grating 504 can be similar in construction as the analyzer grating 514 and arranged similarly at a shallow angle as described above with respect to the analyzer grating 514, although placed at a different position along the optical axis.
- to block X-rays is intended to mean that sufficient attenuation is achieved relative to X-rays that pass through the optically rare regions of the grating to permit a useful contrast for the particular application. It is not intended to require absolutely 100% attenuation.
- the splitter grating 504 and the analyzer grating 514 are arranged with a separation determined according to Talbot-Lau conditions according to some embodiments of the present disclosure.
- the splitter grating 504 and the analyzer grating 514 have grating patterns that are determined according to Talbot-Lau conditions.
- the X-ray illumination system 502 can include an X-ray source 516, and a source grating 518 arranged in an optical path between the X-ray source 516 and the beam splitter 104.
- the source grating 518 provides a plurality of substantially coherent X-ray beams when X-ray source 516 is a spatially extended source of X-rays, as is illustrated schematically in FIG. 5.
- the X-ray illumination system 502 can include combinations of one or more gratings and mirrors, including both transmission and/or reflection gratings.
- the source grating 518 and the analyzer grating 514 are absorption gratings made of Au.
- a limitation in the glancing angle design is that inclining the gratings reduces also the field of view in the vertical direction by of factor of sin(a).
- the achievable vertical field of view is -12-40 mm for angles in the 10-30° range.
- a limitation common to all grating interferometers is that the horizontal field of view is reduced (vignetted) by the narrow (few ⁇ ), but deep (-100 ⁇ ) grating openings. At glancing incidence this effect is more pronounced due to the increased effective depth of the openings.
- the gratings were made by MicroWorks Inc., Germany in 0.2-0.5 mm thick Si wafers and had 70 mm diameter.
- a W anode tube (1 mA/50 ⁇ spot) was used at 60-80 kVp and immersed the samples to be imaged in a water bath having thickness between 70 and 200 mm. These conditions were meant to simulate imaging of a large joint such as the knee, while using relatively small test samples (the field of view of the interferometer at the sample being limited to 25 mm by the detector size and the 1.7 object magnification). The samples were positioned -150 mm behind the phase grating.
- the detector was a 150 ⁇ thick, 42x42 mm CsLTl scintillator, viewed by a 36x36 mm, 64-bit cooled CCD, through an f/l relay lens system.
- the spatial resolution of the X-ray imaging system at the sample was ⁇ 75 ⁇ .
- the low efficiency of the lens coupled detector and the low current of the X-ray tube required using long exposures (30-40s) to acquire sufficient photon statistics.
- the large increase in contrast at high energy with the glancing angle interferometer is illustrated in FIGS. 6A and 6B.
- FIGS. 6A and 6B illustrate the Moire fringe contrast obtained with the 5.4 ⁇ interferometer and a 43 keV mean energy spectrum, at normal and at 18° incidence.
- the beam-splitter was an 8.5 ⁇ thick Au grating, and at glancing incidence a 7 ⁇ thick Ni grating.
- the glancing angle interferometer has several times the contrast of the normal incidence one.
- the spectrum was filtered with 2 mm Al, 0.65 ⁇ Cu, and 200 mm water, to obtain a mean energy of ⁇ 58 keV.
- the 40-60 keV range of mean energies is particularly difficult for Talbot-Lau interferometry, because the Au X-ray absorption is low below 80 keV.
- the glancing angle setup enabled nevertheless achieving over 30% contrast even in this difficult region.
- FIGS. 6A, 6B, and 6C the field of view vignetting at glancing incidence is illustrated in FIG. 7, which plots the horizontal intensity profile obtained with the 10 ⁇ interferometer at 80 kVp/55 keV and at 10° glancing angle.
- the FWHM of the profile is only ⁇ 18 mm.
- the X-ray transmission of the glancing incidence interferometer is in the 20% range, for instance -21% peak transmission with the 5.4 ⁇ interferometer at 18°, for a spectrum with 55 keV mean energy.
- the transmission could be increased by several percent using thinner grating substrates than in experiments.
- a phantom consisting of concentric cylindrical layers of water, PMMA, Al and nylon, simulating joint fluid, cartilage, cortical, and trabecular bone, respectively, was used, as illustrated in FIG. 8.
- a phantom consisting of concentric cylindrical layers of water, PMMA, Al and nylon, simulating joint fluid, cartilage, cortical, and trabecular bone, respectively.
- Cone-beam CT images of the phantom were obtained at 60 kVp/43 keV mean energy with the 5.4 ⁇ period interferometer at 30° and are illustrated in FIG. 8.
- the data was obtained using 200 CT angles with 1° step, 8 phase steps per angle and 30s exposure per step.
- the results show that DPC-CT has superior discrimination capability for soft tissue like materials at high energy. For instance, DPC-CT discriminates PMMA (cartilage) from water, while attenuation CT does not.
- the nylon/water, and in particular the nylon/PMMA contrast is also superior in DPC-CT.
- fine details such as the thin interfaces between the layers have better contrast in DPC-CT.
- the 80 kVp DPC radiograph of the phantom immersed in 200 mm water also shows superior contrast compared to the attenuation one: the PMMA layer is discriminated in the DPC image but not in the attenuation one, and the nylon/water contrast is also strongly increased.
- the high contrast of the glancing angle interferometer at high energy makes nevertheless possible phase contrast imaging in the presence of bone. The reason is twofold. First, at high enough energy the bone scatter decreases. Secondly, the initial contrast of the glancing angle interferometer is high enough that even after traversing a thick bone layer the X-rays remain sufficiently coherent to allow phase contrast imaging. This point is illustrated in FIGS.
- the glancing angle interferometer enabled also obtaining first DPC-CT images of a human joint with energetic X-ray spectra. Due to field of view limitations a human finger PIP joint of ⁇ 23 mm diameter was used, immersed in a 25 mm plastic vial. The vial was filled with a 60%-40% water ethanol mixture to preserve the tissue and further immersed in a thick water bath to produce an energetic transmitted spectrum. The CT parameters were the same as for the joint phantom experiments. [0061] FIG. 10 shows DPC-CT and attenuation CT images of the joint, obtained with the 5.4 ⁇ and the 10 ⁇ glancing angle interferometers at 60 and 80 kVp.
- the DPC-CT image shows soft tissue contrast at both 60 kVp and 80 kVp, while the attenuation CT image does not at either energy.
- the combination of soft tissue contrast and high spatial resolution in DPC-CT enables visualizing anatomical detail such as the flexor tendon (FT), the volar plate (FP), or the extensor digitorum communis (EDC).
- the 80 kVp DPC image has somewhat less soft tissue contrast compared to the 60 kVp one, as expected from the decrease in refraction angles with energy and from the lower angular sensitivity of the 10 ⁇ interferometer compared to the 5.4 ⁇ one.
- the knee joint would be a good place to start studying clinical DPC imaging, because the knee can be kept fixed for relatively long periods of time and because physiological movement is less of an issue.
- a DPC-CT system for the knee should work in principle with a spectrum and patient exposure similar to that in conventional CT (80-90 kVp and ⁇ few hundred mA-s per scan, respectively).
- the glancing angle interferometer solves the problem of the high energy contrast. Further on, the vertical field of view limitation of this instrument may be less constraining for knee CT, because imaging a 20-25 mm vertical region-of-interest centered on the joint space may be sufficient for most diagnostic purposes. However, the horizontal FOV must be much larger. Assuming a typical knee diameter of -150 mm and an object magnification around 1.5, a FOV >220 mm would be needed at the detector for full cone- beam CT. The strong lateral vignetting of the glancing angle interferometer prevents however covering more than 10-20 mm with a single grating, as illustrated in FIG. 7.
- FIG. 4 shows an example implementation of the tiled grating GAI interferometer that includes using multiple 'sub-gratings' with slightly rotated lines, made on a single substrate or wafer. All the sub-gratings have equal period and width; the width is equal or less than the FWHM of their vignetting curve (e.g., 10 mm for a 10 ⁇ period grating at 10° angle).
- the rotation angle follows the central ray direction for each sub-grating. In this way the incident X-rays 'see' an array of collimators that are with good approximation aligned to the ray direction, thus minimizing the vignetting.
- a 6" Si wafer would accommodate 12 sub-gratings of 10 mm width and 90 mm height, giving a FOV at the detector of 120 mm width and 30 mm height, at a glancing angle of 20°.
- Two such wafers side by side would cover a contiguous FOV 240 mm wide, sufficient for full cone-beam CT.
- An advantage of the above example implementation is that the sub-gratings are aligned with nanometer precision through the lithographic manufacturing process, thus avoiding the need for complex and costly positioning systems.
- FIG. 3 shows Moire fringes obtained in this setup, confirming that high interferometer contrast is obtained also with the gratings positioned far from the on-axis position.
- the tiled grating glancing angle interferometer offers a path towards the development of high energy DPC systems, such as for knee CT.
- DPC systems such as for knee CT.
- the X-ray source may have a spot size in the 100 ⁇ range.
- it may provide sufficient intensity to compensate the interferometer attenuation, and it may operate for extended periods because the DPC-CT scan times will likely be longer than in conventional CT.
- Such tubes nevertheless exist and could be adapted for clinical DPC-CT.
- microfocus rotating anode tubes have been developed for protein
- crystallography that have 70 ⁇ spot size and can operate continuously at several kW power.
- Detectors having simultaneously low noise, high efficiency and sensitivity, and large FOV in one dimension will also be needed.
- An example of such a detector is the ARGUS X-ray CCD developed by DALSA for panoramic dental imaging, which has a high resolution scintillator directly coupled to a 210 mm wide CCD.
- the high sensitivity and low noise of a direct coupled and cooled CCD would also help achieving high spatial resolution at acceptable patient dose.
- Photon counting detectors could be another option.
- DPC-CT should not require a higher X-ray flux than conventional CT. Due to the several fold intensity decrease in the gratings the scan time will be however inherently longer. In order to minimize the dose and scan time it will be thus important to try and apply to DPC-CT novel image reconstruction methods developed for conventional CT, such as model-based statistical reconstruction, sparse sampling, or compressed sensing, as are known in the art.
Landscapes
- Health & Medical Sciences (AREA)
- Physics & Mathematics (AREA)
- Life Sciences & Earth Sciences (AREA)
- Chemical & Material Sciences (AREA)
- General Physics & Mathematics (AREA)
- Pathology (AREA)
- General Health & Medical Sciences (AREA)
- Analytical Chemistry (AREA)
- Biochemistry (AREA)
- Immunology (AREA)
- Engineering & Computer Science (AREA)
- Crystallography & Structural Chemistry (AREA)
- Optics & Photonics (AREA)
- Medical Informatics (AREA)
- Radiology & Medical Imaging (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- High Energy & Nuclear Physics (AREA)
- Biophysics (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Theoretical Computer Science (AREA)
- Pulmonology (AREA)
- Apparatus For Radiation Diagnosis (AREA)
- Analysing Materials By The Use Of Radiation (AREA)
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2015557243A JP2016509872A (en) | 2014-02-10 | 2014-04-09 | Large field grating interferometer for X-ray phase contrast imaging and CT at high energy |
KR1020157025056A KR20160014576A (en) | 2013-02-12 | 2014-04-09 | Large field of view grating interferometers for x-ray phase contrast imaging and ct at high energy |
CN201480008497.XA CN105142524A (en) | 2014-02-10 | 2014-04-09 | Large field of view grating interferometers for x-ray phase contrast imaging and ct at high energy |
EP14757381.0A EP2956064A4 (en) | 2013-02-12 | 2014-04-09 | Large field of view grating interferometers for x-ray phase contrast imaging and ct at high energy |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US201361763683P | 2013-02-12 | 2013-02-12 | |
US61/763,683 | 2013-02-12 | ||
US14/176,655 US9329141B2 (en) | 2013-02-12 | 2014-02-10 | Large field of view grating interferometers for X-ray phase contrast imaging and CT at high energy |
US14/176,655 | 2014-02-10 |
Publications (2)
Publication Number | Publication Date |
---|---|
WO2014134634A2 true WO2014134634A2 (en) | 2014-09-04 |
WO2014134634A3 WO2014134634A3 (en) | 2014-12-04 |
Family
ID=51297425
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2014/033561 WO2014134634A2 (en) | 2013-02-12 | 2014-04-09 | Large field of view grating interferometers for x-ray phase contrast imaging and ct at high energy |
PCT/US2015/011082 WO2015119747A1 (en) | 2013-02-12 | 2015-01-13 | System and method for phase-contrast x-ray imaging |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2015/011082 WO2015119747A1 (en) | 2013-02-12 | 2015-01-13 | System and method for phase-contrast x-ray imaging |
Country Status (4)
Country | Link |
---|---|
US (2) | US9439613B2 (en) |
EP (1) | EP2956064A4 (en) |
KR (1) | KR20160014576A (en) |
WO (2) | WO2014134634A2 (en) |
Families Citing this family (48)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2010134012A1 (en) * | 2009-05-19 | 2010-11-25 | Koninklijke Philips Electronics N.V. | Grating for phase-contrast imaging |
US20150117599A1 (en) * | 2013-10-31 | 2015-04-30 | Sigray, Inc. | X-ray interferometric imaging system |
WO2014137318A1 (en) * | 2012-03-05 | 2014-09-12 | University Of Rochester | Methods and apparatus for differential phase-contrast cone-beam ct and hybrid cone-beam ct |
US9532760B2 (en) * | 2012-04-24 | 2017-01-03 | Siemens Aktiengesellschaft | X-ray device |
US9907524B2 (en) | 2012-12-21 | 2018-03-06 | Carestream Health, Inc. | Material decomposition technique using x-ray phase contrast imaging system |
US10578563B2 (en) | 2012-12-21 | 2020-03-03 | Carestream Health, Inc. | Phase contrast imaging computed tomography scanner |
US9357975B2 (en) * | 2013-12-30 | 2016-06-07 | Carestream Health, Inc. | Large FOV phase contrast imaging based on detuned configuration including acquisition and reconstruction techniques |
US9001967B2 (en) * | 2012-12-28 | 2015-04-07 | Carestream Health, Inc. | Spectral grating-based differential phase contrast system for medical radiographic imaging |
US9494534B2 (en) | 2012-12-21 | 2016-11-15 | Carestream Health, Inc. | Material differentiation with phase contrast imaging |
US10096098B2 (en) | 2013-12-30 | 2018-10-09 | Carestream Health, Inc. | Phase retrieval from differential phase contrast imaging |
US9724063B2 (en) | 2012-12-21 | 2017-08-08 | Carestream Health, Inc. | Surrogate phantom for differential phase contrast imaging |
US9700267B2 (en) | 2012-12-21 | 2017-07-11 | Carestream Health, Inc. | Method and apparatus for fabrication and tuning of grating-based differential phase contrast imaging system |
AU2012268876A1 (en) * | 2012-12-24 | 2014-07-10 | Canon Kabushiki Kaisha | Non-linear solution for 2D phase shifting |
US9439613B2 (en) * | 2013-02-12 | 2016-09-13 | The Johns Hopkins University | System and method for phase-contrast X-ray imaging |
US10085701B2 (en) * | 2013-07-30 | 2018-10-02 | Konica Minolta, Inc. | Medical image system and joint cartilage state score determination method |
US10269528B2 (en) | 2013-09-19 | 2019-04-23 | Sigray, Inc. | Diverging X-ray sources using linear accumulation |
US10416099B2 (en) | 2013-09-19 | 2019-09-17 | Sigray, Inc. | Method of performing X-ray spectroscopy and X-ray absorption spectrometer system |
US10295485B2 (en) | 2013-12-05 | 2019-05-21 | Sigray, Inc. | X-ray transmission spectrometer system |
US10297359B2 (en) | 2013-09-19 | 2019-05-21 | Sigray, Inc. | X-ray illumination system with multiple target microstructures |
USRE48612E1 (en) | 2013-10-31 | 2021-06-29 | Sigray, Inc. | X-ray interferometric imaging system |
US10304580B2 (en) | 2013-10-31 | 2019-05-28 | Sigray, Inc. | Talbot X-ray microscope |
US9936935B1 (en) * | 2014-02-14 | 2018-04-10 | Nosil DSC Innovations, Inc. | Phantom systems and methods for diagnostic radiographic and fluoroscopic X-ray equipment |
CN106659444B (en) * | 2014-05-09 | 2020-02-21 | 约翰斯·霍普金斯大学 | System and method for phase contrast X-ray imaging |
US10401309B2 (en) | 2014-05-15 | 2019-09-03 | Sigray, Inc. | X-ray techniques using structured illumination |
JP6451400B2 (en) * | 2015-02-26 | 2019-01-16 | コニカミノルタ株式会社 | Image processing system and image processing apparatus |
US10352880B2 (en) | 2015-04-29 | 2019-07-16 | Sigray, Inc. | Method and apparatus for x-ray microscopy |
EP3314576B1 (en) | 2015-06-26 | 2019-11-27 | Koninklijke Philips N.V. | Robust reconstruction for dark-field and phase contrast ct |
US10295486B2 (en) | 2015-08-18 | 2019-05-21 | Sigray, Inc. | Detector for X-rays with high spatial and high spectral resolution |
EP3510563B1 (en) | 2016-09-08 | 2021-11-10 | Koninklijke Philips N.V. | Improved phase-contrast and dark-field ct reconstruction algorithm |
US10247683B2 (en) | 2016-12-03 | 2019-04-02 | Sigray, Inc. | Material measurement techniques using multiple X-ray micro-beams |
CN110049727B (en) | 2016-12-06 | 2023-12-12 | 皇家飞利浦有限公司 | Interferometer grating support for grating-based X-ray imaging and/or support bracket therefor |
US10578566B2 (en) | 2018-04-03 | 2020-03-03 | Sigray, Inc. | X-ray emission spectrometer system |
US10989822B2 (en) | 2018-06-04 | 2021-04-27 | Sigray, Inc. | Wavelength dispersive x-ray spectrometer |
WO2020023408A1 (en) | 2018-07-26 | 2020-01-30 | Sigray, Inc. | High brightness x-ray reflection source |
EP3603515A1 (en) | 2018-08-01 | 2020-02-05 | Koninklijke Philips N.V. | Apparatus for generating x-ray imaging data |
US10656105B2 (en) | 2018-08-06 | 2020-05-19 | Sigray, Inc. | Talbot-lau x-ray source and interferometric system |
DE112019004433T5 (en) | 2018-09-04 | 2021-05-20 | Sigray, Inc. | SYSTEM AND PROCEDURE FOR X-RAY FLUORESCENCE WITH FILTERING |
WO2020051221A2 (en) | 2018-09-07 | 2020-03-12 | Sigray, Inc. | System and method for depth-selectable x-ray analysis |
DE112019006010T5 (en) * | 2018-12-03 | 2021-08-19 | The University Of North Carolina At Chapel Hill | COMPACT X-RAY DEVICES, SYSTEMS, AND PROCEDURES FOR TOMOSYNTHESIS, FLUOROSCOPY, AND STEREOTACTIC IMAGING |
US11006912B2 (en) * | 2019-03-25 | 2021-05-18 | Battelle Memorial Institute | Methods, systems, and computer-readable storage media for enhanced phase-contrast x-ray imaging |
US11639903B2 (en) | 2019-03-25 | 2023-05-02 | Battelle Memorial Institute | Serial Moire scanning phase contrast x-ray imaging |
US11143605B2 (en) | 2019-09-03 | 2021-10-12 | Sigray, Inc. | System and method for computed laminography x-ray fluorescence imaging |
US11175243B1 (en) | 2020-02-06 | 2021-11-16 | Sigray, Inc. | X-ray dark-field in-line inspection for semiconductor samples |
DE112021002841T5 (en) | 2020-05-18 | 2023-03-23 | Sigray, Inc. | System and method for X-ray absorption spectroscopy using a crystal analyzer and multiple detector elements |
JP2023542674A (en) | 2020-09-17 | 2023-10-11 | シグレイ、インコーポレイテッド | System and method for depth-resolved measurement and analysis using X-rays |
KR20230109735A (en) | 2020-12-07 | 2023-07-20 | 시그레이, 아이엔씨. | High-throughput 3D x-ray imaging system using transmitted x-ray source |
US11992350B2 (en) | 2022-03-15 | 2024-05-28 | Sigray, Inc. | System and method for compact laminography utilizing microfocus transmission x-ray source and variable magnification x-ray detector |
WO2023215204A1 (en) | 2022-05-02 | 2023-11-09 | Sigray, Inc. | X-ray sequential array wavelength dispersive spectrometer |
Family Cites Families (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4798446A (en) | 1987-09-14 | 1989-01-17 | The United States Of America As Represented By The United States Department Of Energy | Aplanatic and quasi-aplanatic diffraction gratings |
US5812629A (en) | 1997-04-30 | 1998-09-22 | Clauser; John F. | Ultrahigh resolution interferometric x-ray imaging |
US6804324B2 (en) | 2001-03-01 | 2004-10-12 | Osmo, Inc. | X-ray phase contrast imaging using a fabry-perot interferometer concept |
US7315611B2 (en) | 2003-06-03 | 2008-01-01 | Monochromatic X-Ray Technologies, Inc. | X-ray reflector exhibiting taper, method of making same, narrow band x-ray filters including same, devices including such filters, multispectral x-ray production via unispectral filter, and multispectral x-ray production via multispectral filter |
EP1731099A1 (en) | 2005-06-06 | 2006-12-13 | Paul Scherrer Institut | Interferometer for quantitative phase contrast imaging and tomography with an incoherent polychromatic x-ray source |
DE102006037281A1 (en) | 2006-02-01 | 2007-08-09 | Siemens Ag | X-ray radiographic grating of a focus-detector arrangement of an X-ray apparatus for generating projective or tomographic phase-contrast images of an examination subject |
US7659529B2 (en) * | 2007-04-13 | 2010-02-09 | Cymer, Inc. | Method and apparatus for vibration reduction in laser system line narrowing unit wavelength selection optical element |
US7949095B2 (en) * | 2009-03-02 | 2011-05-24 | University Of Rochester | Methods and apparatus for differential phase-contrast fan beam CT, cone-beam CT and hybrid cone-beam CT |
JP2010253194A (en) | 2009-04-28 | 2010-11-11 | Fujifilm Corp | Radiation phase imaging apparatus |
EP2442722B1 (en) | 2009-06-16 | 2017-03-29 | Koninklijke Philips N.V. | Correction method for differential phase contrast imaging |
JP5238786B2 (en) | 2010-10-26 | 2013-07-17 | 富士フイルム株式会社 | Radiography apparatus and radiation imaging system |
CA2843311C (en) * | 2011-07-29 | 2016-06-07 | The Johns Hopkins University | Differential phase contrast x-ray imaging system and components |
WO2013096974A1 (en) * | 2011-12-21 | 2013-06-27 | THE UNITED STATES OF AMERICA, as represented by THE SECRETARY DEPT. OF HEALTH AND HUMAN SERVICES | Multilayer-coated micro grating array for x-ray phase sensitive and scattering sensitive imaging |
US9439613B2 (en) * | 2013-02-12 | 2016-09-13 | The Johns Hopkins University | System and method for phase-contrast X-ray imaging |
-
2014
- 2014-02-06 US US14/174,830 patent/US9439613B2/en active Active
- 2014-02-10 US US14/176,655 patent/US9329141B2/en not_active Expired - Fee Related
- 2014-04-09 WO PCT/US2014/033561 patent/WO2014134634A2/en active Application Filing
- 2014-04-09 EP EP14757381.0A patent/EP2956064A4/en not_active Withdrawn
- 2014-04-09 KR KR1020157025056A patent/KR20160014576A/en not_active Application Discontinuation
-
2015
- 2015-01-13 WO PCT/US2015/011082 patent/WO2015119747A1/en active Application Filing
Non-Patent Citations (1)
Title |
---|
STUTMAN D ET AL.: "APPLIED PHYSICS LETTERS", vol. 101, A I P PUBLISHING LLC, article "Glancing angle Talbot-Lau grating interferometers for phase contrast imaging at high x-ray energy", pages: 91108 |
Also Published As
Publication number | Publication date |
---|---|
EP2956064A4 (en) | 2016-11-09 |
WO2015119747A1 (en) | 2015-08-13 |
EP2956064A2 (en) | 2015-12-23 |
WO2014134634A3 (en) | 2014-12-04 |
KR20160014576A (en) | 2016-02-11 |
US9439613B2 (en) | 2016-09-13 |
US20140226782A1 (en) | 2014-08-14 |
US9329141B2 (en) | 2016-05-03 |
US20140226785A1 (en) | 2014-08-14 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US9329141B2 (en) | Large field of view grating interferometers for X-ray phase contrast imaging and CT at high energy | |
JP5702586B2 (en) | Radiography system | |
US8972191B2 (en) | Low dose single step grating based X-ray phase contrast imaging | |
US7433444B2 (en) | Focus-detector arrangement of an X-ray apparatus for generating projective or tomographic phase contrast recordings | |
RU2145485C1 (en) | Ultrasmall-angle roentgen tomography | |
JP5961614B2 (en) | Grating apparatus for phase contrast imaging, apparatus for phase contrast imaging, X-ray system having the apparatus, and method of using the apparatus | |
JP5238786B2 (en) | Radiography apparatus and radiation imaging system | |
US20100166139A1 (en) | Effective dual-energy x-ray attenuation measurement | |
JP2012090945A (en) | Radiation detection device, radiographic apparatus, and radiographic system | |
JP2012090944A (en) | Radiographic system and radiographic method | |
EP2789296A1 (en) | Radiography apparatus | |
WO2009064495A2 (en) | Schlieren-type radiography using a line source and focusing optics | |
JP5665834B2 (en) | X-ray imaging device | |
JP2019537482A (en) | Apparatus for generating multi-energy data from phase contrast imaging data | |
WO2012057047A1 (en) | Radiation imaging system | |
JP2016509872A (en) | Large field grating interferometer for X-ray phase contrast imaging and CT at high energy | |
JP7167201B2 (en) | X-ray phase detector | |
JP2014155508A (en) | Radiographic system | |
Stutman et al. | High energy x-ray phase-contrast imaging using glancing angle grating interferometers | |
WO2012056992A1 (en) | Radiograph detection device, radiography device, radiography system | |
JP2012228369A (en) | Radiographic system, and radiographic method | |
Pyakurel | Phase and dark field radiography and CT with mesh-based structured illumination and polycapillary optics | |
WO2012057045A1 (en) | X-ray imaging device, x-ray imaging system | |
JP2012125364A (en) | Radiation image detector, radiographic apparatus, and radiographic system | |
Graeff | Biomedical application of microtomography |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
WWE | Wipo information: entry into national phase |
Ref document number: 201480008497.X Country of ref document: CN |
|
ENP | Entry into the national phase |
Ref document number: 2015557243 Country of ref document: JP Kind code of ref document: A |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2014757381 Country of ref document: EP |
|
ENP | Entry into the national phase |
Ref document number: 20157025056 Country of ref document: KR Kind code of ref document: A |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 14757381 Country of ref document: EP Kind code of ref document: A2 |