WO2010109368A1 - Differential phase-contrast imaging with circular gratings - Google Patents

Differential phase-contrast imaging with circular gratings Download PDF

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Publication number
WO2010109368A1
WO2010109368A1 PCT/IB2010/051098 IB2010051098W WO2010109368A1 WO 2010109368 A1 WO2010109368 A1 WO 2010109368A1 IB 2010051098 W IB2010051098 W IB 2010051098W WO 2010109368 A1 WO2010109368 A1 WO 2010109368A1
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WO
WIPO (PCT)
Prior art keywords
grating
phase
source
imaging apparatus
phase grating
Prior art date
Application number
PCT/IB2010/051098
Other languages
French (fr)
Inventor
Ewald Roessl
Thomas Koehler
Gerhard Martens
Original Assignee
Koninklijke Philips Electronics N.V.
Philips Intellectual Property & Standards Gmbh
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 Koninklijke Philips Electronics N.V., Philips Intellectual Property & Standards Gmbh filed Critical Koninklijke Philips Electronics N.V.
Priority to EP10710906A priority Critical patent/EP2410921A1/en
Priority to JP2012501436A priority patent/JP5705826B2/en
Priority to US13/260,380 priority patent/US9269471B2/en
Priority to CN201080013839.9A priority patent/CN102365052B/en
Publication of WO2010109368A1 publication Critical patent/WO2010109368A1/en

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    • 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
    • G21K7/00—Gamma- or X-ray microscopes
    • 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
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid 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
    • 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
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/502—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of breast, i.e. mammography

Definitions

  • the invention relates to phase-contrast imaging.
  • the invention relates to a phase-contrast imaging apparatus for examining an object of interest, a method of phase-contrast imaging, a computer-readable medium and a program element.
  • X-rays For examination of objects of interest with electromagnetic radiation, visible or invisible light or X-rays may be used.
  • the method disclosed in Pfeiffer et al. “Phase retrieval and differential phase-contrast imaging with low-brilliance X-ray sources", Nature Physics 2006 in the domain of X-ray differential phase-contrast imaging (DPC) is based on an extension of Talbot interferometry.
  • the extension consists of adding a third grating allowing the use of a poly-chromatic X-ray spectrum.
  • the gratings used in this technique are formed by linear trench arrangements, as depicted in Figs. 1 and 2.
  • the detection of intensity variations via phase stepping allows the measurement of the phase gradient of the X-ray wave front perpendicular to the trenches of the grating.
  • the invention relates to a phase-contrast imaging apparatus for examining an object of interest, a method of phase-contrast imaging, a computer-readable medium and a program element according to the features of the independent claims. Further features of exemplary embodiments of the invention are stated in the dependent claims. It should be noted that the features which are in the following described for example with respect to the imaging apparatus may also be implemented as method steps in the method, the computer-readable medium or the program element, and vice versa.
  • a phase-contrast imaging apparatus for examining an object of interest
  • the apparatus comprising a source for emitting a beam of radiation, a detector and a phase grating positioned between the source and the detector.
  • the detector is adapted for detecting the radiation after it has passed the object of interest and the phase grating, wherein the phase grating has a curved geometry.
  • all gratings used in the imaging apparatus have such a curved geometry.
  • the term "curved geometry" refers to a phase grating geometry which is not linear but comprises arcuated or bended structures, such as circles or segments of a circle or any.
  • the phase grating has one of a circular geometry and a spiral geometry.
  • the phase grating (and for example both absorption gratings as well) comprise concentrically arranged trenches or a helical, i.e. spiral-like trench.
  • the beam of radiation emitted by the source is a cone-beam.
  • the imaging apparatus is designed in cone-beam symmetry.
  • a linear grating arrangement breaks the cone-beam symmetry of the imaging system.
  • the above and in the following described gratings respect the above-mentioned symmetry, thus yielding a couple of advantages.
  • gratings with a curved geometry for example spiral or circular gratings
  • phase retrieval may be simplified due to common-ground truth "phase point on the optical axis”.
  • the cylindrical symmetry may avoid edge distortions.
  • the above and the in the following described setup may provide a viable alternative to other DPC techniques using linear gratings.
  • the imaging apparatus further comprises a second grating which is adapted in form of an absorption grating positioned in front of the detector.
  • the second grating has a curved geometry as well and has a pitch different from the pitch of the first phase grating.
  • the imaging apparatus further comprises a third grating which is an absorption grating positioned between the source and the object of interest and which also has a curved geometry.
  • the third grating has a third pitch which is different from the first pitch of the phase grating and allows for an essentially coherent illumination of the phase grating.
  • the imaging apparatus further comprises a stepper motor.
  • the beam of radiation emitted by the source has an optical axis, wherein the stepper motor is adapted for moving at least one of the phase grating and the second (absorption) grating along the optical axis of the beam of radiation emitted by the source.
  • the imaging apparatus may be adapted in such a way that the focal spot of the beam of radiation emitted by the source moves along the optical axis during image acquisition.
  • the imaging apparatus further comprises a rotating motor, wherein the rotating motor is adapted for rotating at least one of the phase grating and the second grating around the optical axis of the beam of radiation.
  • the phase grating Gl and/or the second absorption grating G2 are adapted in spiral geometry and positioned on the optical axis.
  • one or each of the two gratings Gl, G2 is positioned offset of the optical axis and rotated around the optical axis.
  • the pitch of the phase grating (104) is not constant but a function of a distance from the center of the phase grating.
  • the pitch may increase with increasing distance from the center. This may be also the case for the absorption gratings GO and G2. This may be useful to simplify the phase-stepping procedure along the optical axis.
  • the source is an X-ray source, wherein the apparatus is adapted as an X-ray based differential phase contrast imaging apparatus.
  • the source is a light source
  • the imaging apparatus is adapted as an optical imaging apparatus where the beam of radiation used for probing the object is an optical radiation beam with a wavelength within the range of for example 400 to 1400 nm.
  • a method of phase-contrast imaging for examining an object of interest in which a beam of radiation is emitted by a source. Furthermore, a phase grating is positioned between the source and the detector. Phase stepping is performed along the optical axis with a focal spot, the phase grating and/or the absorber grating. Furthermore, radiation is detected by the detector after it has passed the object of interest and the phase grating, wherein the phase grating has a curved geometry.
  • a radial outward integration of the detected radiation is performed for phase retrieval.
  • at least one of the phase grating, a second grating, which is an absorption grating positioned in front of the detector and having a curved geometry, and a focal spot of the beam of radiation emitted by the source is moved along an optical axis of the beam.
  • At least one of the phase grating, the second grating and the beam of radiation emitted by the source is rotated around an optical axis of the beam.
  • a computer-readable medium in which a computer program for examination of an object of interest is stored which, when executed by a processor of an imaging apparatus causes the imaging apparatus to carry out the above-mentioned method steps.
  • a program element for examination of an object of interest is provided, which, when being executed by a processor of an imaging apparatus, causes the imaging apparatus to carry out the above-mentioned method steps.
  • phase stepping reveals the phase gradient along the Cartesian stepping direction.
  • the phase stepping is performed along the optical axis with the focal spot, the phase grating or the absorber grating.
  • the measured signal is the phase-gradient in the radial direction.
  • the required positioning accuracy along the optical axis may be comparatively low compared to the relatively high accuracy required for the stepping in the case of linear gratings.
  • FIG. IA shows a measurement setup with three linear gratings.
  • Fig. IB shows a cross-sectional view of the setup of Fig. IA.
  • Fig. 2A shows a linear phase grating.
  • Fig. 2B shows a linear absorption grating.
  • Fig. 3 shows a measurement setup according to an exemplary embodiment of the invention.
  • Fig. 4 shows an imaging system according to an exemplary embodiment of the invention.
  • Fig. 5 shows a flow-chart of a method according to an exemplary embodiment of the invention.
  • Fig. IA shows a measurement setup for differential phase-contrast imaging with linear gratings.
  • An incoherent X-ray source is used which is symbolized by the focal spot 101.
  • the radiation beam emitted by the source has an optical axis 4.
  • the beam passes the absorption grating 1 (Go).
  • the beam passes the object of interest 103 and then the phase grating 2 (Gi).
  • the beam passes a second absorption grating 3 (G2), which is arranged before the imaging detector 102.
  • Reference numeral 5 depicts the x-axis
  • reference numeral 6 the y-axis
  • reference numeral 7 the z-axis, which is arranged parallel to the optical axis 4.
  • Fig. IB shows a cross-sectional view of the setup depicted in Fig. IA.
  • the focal spot of the source 101 has a width W, which is usually much bigger than the pitch po of the first absorption grating 1 (see reference numeral 8).
  • the phase grating 2 is arranged a distance 1 from the first absorption grating 1. Between the first absorption grating 1 and the phase grating 2 is the object of interest 103.
  • the second absorption grating 3 is arranged a distance d from the phase grating 2, which has a pitch 10 (P 2 ) which is smaller than the pitch of the first absorption grating 1.
  • the phase grating 2 has a pitch 9 (pi) which allows that radiation from the source which has a certain energy E produces a Talbot image at the imaging detector 102.
  • Figs. 2A and 2B each show a section of the linear gratings 2 and 3, respectively.
  • Fig. 3 shows a filter and detector setup for an imaging apparatus according to an exemplary embodiment of the invention.
  • the imaging setup has three circular gratings, i.e. an absorption grating 106 arranged after the focal spot of the source 101, a phase grating 104 arranged after the object of interest 103 and a second absorption grating 105 arranged before the detector 102.
  • the second absorption grating 105 can be moved or stepped along the optical axis 4. It should be noted, that the pitches of the circular (or spiral) gratings 104, 105 and 106 are not to scale. With respect to the system disclosed by Pfeiffer et al. all linear gratings are replaced by circular gratings (or spiral gratings) and the phase stepping is performed along the optical axis. The method is sensitive to the radial phase gradient.
  • the source grating 106 is adapted to guarantee essentially ,,coherent" illumination of the phase grating 104.
  • the distortions of the Talbot self-image (Fourier image) generated by the phase object 103 are analyzed by the absorption grating 105 through stepping along the optical axis 4.
  • the detector measures the local phase- gradient in the radial direction. For phase-retrieval radial outward integrations are performed with the advantage of having a common "anchor" for the wave front phase.
  • the trenches of the gratings are not realized in the form of concentric rings but are realized as spirals.
  • the phase stepping may then be implemented via a rotation of one of the gratings around the optical axis by an angle of 360 degrees.
  • a second phase grating (such as phase grating 410 of Fig. 4) may be positioned next to the first phase grating 104 in order to produce a second Talbot image at the detector.
  • the imaging system may either be an X-ray imaging system or an optical imaging system.
  • Fig. 4 shows an imaging system 400 according to an exemplary embodiment of the invention.
  • the imaging system depicted in Fig. 4 may be adapted in form of a mammography imaging system.
  • the object of interest 103 may be a breast of a patient which is disposed between the two pressure plates 401, 402 for applying pressure to the patient's breast.
  • the source 101 may an X-ray source or, for instance, an optical energy source (in which case the system may be used for other purposes).
  • the radiation emitted by the source 101 first passes the grating 106 and then the object of interest to be imaged 103.
  • phase gratings may be integrated in a corresponding housing and may thus form a module.
  • the module is connected to the control unit 403 such that the gratings 104, 410 can be moved upwards and downwards along arrows 308, 309.
  • a second absorption grating 105 is positioned before the detector 102.
  • Each of the gratings can be connected to the same or a respective individual motor 408 for moving the gratings along the arrows 308, 309 and/or for rotating the gratings around the optical axis 4.
  • Both the source 101 and the detector 102 are connected to the control unit 403 via lines 405, 406, respectively.
  • the detector 102 comprises a Talbot interferometer 408.
  • a data line 407 connects the control unit 403 to an input and output device 404, which can be used for inputting control information for controlling the imaging system 400 and which can also be used for outputting visual information relating to the final image.
  • Fig. 5 shows a flow-chart of a method according to an exemplary embodiment of the invention.
  • a beam of radiation is emitted by a source, for example an X-ray source emitting polychromatic x-rays.
  • a source for example an X-ray source emitting polychromatic x-rays.
  • the phase grating or the absorption grating at the detector are stepped, i.e. moved along the optical axis. In case spiral gratings are used, a rotation is performed instead of the linear movement.
  • step 503 the radiation is detected after it has passed the object of interest and the gratings and in step 504 the phase is retrieved by performing radial outward integrations of the detected signal.
  • the integrations may also be started outside and heading inwards with a necessary condition to arrive at the same value on the optical axis.

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Abstract

The invention relates to an X-ray differential phase-contrast imaging system which has three circular gratings. The circular gratings are aligned with the optical axis of the radiation beam and a phase stepping is performed along the optical axis with the focal spot, the phase grating and/or the absorber grating. The signal measured is the phase-gradient in radial direction away from the optical axis.

Description

DIFFERENTIAL PHASE-CONTRAST IMAGING WITH CIRCULAR GRATINGS
FIELD OF THE INVENTION
The invention relates to phase-contrast imaging. In particular, the invention relates to a phase-contrast imaging apparatus for examining an object of interest, a method of phase-contrast imaging, a computer-readable medium and a program element.
BACKGROUND OF THE INVENTION
For examination of objects of interest with electromagnetic radiation, visible or invisible light or X-rays may be used. The method disclosed in Pfeiffer et al. "Phase retrieval and differential phase-contrast imaging with low-brilliance X-ray sources", Nature Physics 2006 in the domain of X-ray differential phase-contrast imaging (DPC) is based on an extension of Talbot interferometry. The extension consists of adding a third grating allowing the use of a poly-chromatic X-ray spectrum. The gratings used in this technique are formed by linear trench arrangements, as depicted in Figs. 1 and 2. The detection of intensity variations via phase stepping allows the measurement of the phase gradient of the X-ray wave front perpendicular to the trenches of the grating.
However, in order to provide for an image of reasonably well quality, an appropriate positioning accuracy while stepping and a non trivial phase retrieval may have to be performed.
SUMMARY OF THE INVENTION
It may be desirable to provide for an imaging system and method with a more robust possibility for phase retrieval. The invention relates to a phase-contrast imaging apparatus for examining an object of interest, a method of phase-contrast imaging, a computer-readable medium and a program element according to the features of the independent claims. Further features of exemplary embodiments of the invention are stated in the dependent claims. It should be noted that the features which are in the following described for example with respect to the imaging apparatus may also be implemented as method steps in the method, the computer-readable medium or the program element, and vice versa.
According to an exemplary embodiment of the invention, a phase-contrast imaging apparatus for examining an object of interest is provided, the apparatus comprising a source for emitting a beam of radiation, a detector and a phase grating positioned between the source and the detector. The detector is adapted for detecting the radiation after it has passed the object of interest and the phase grating, wherein the phase grating has a curved geometry. For example, all gratings used in the imaging apparatus have such a curved geometry. The term "curved geometry" refers to a phase grating geometry which is not linear but comprises arcuated or bended structures, such as circles or segments of a circle or any.
According to another exemplary embodiment of the invention, the phase grating has one of a circular geometry and a spiral geometry. In other words, the phase grating (and for example both absorption gratings as well) comprise concentrically arranged trenches or a helical, i.e. spiral-like trench.
According to another exemplary embodiment of the invention, the beam of radiation emitted by the source is a cone-beam. Thus, the imaging apparatus is designed in cone-beam symmetry.
With the use of conventional X-ray tube sources, a linear grating arrangement breaks the cone-beam symmetry of the imaging system. The above and in the following described gratings respect the above-mentioned symmetry, thus yielding a couple of advantages. For example, by using gratings with a curved geometry, for example spiral or circular gratings, the requirements on positioning accuracy while stepping may be reduced. Furthermore, phase retrieval may be simplified due to common-ground truth "phase point on the optical axis". Furthermore, the cylindrical symmetry may avoid edge distortions. The above and the in the following described setup may provide a viable alternative to other DPC techniques using linear gratings. According to another exemplary embodiment of the invention, the imaging apparatus further comprises a second grating which is adapted in form of an absorption grating positioned in front of the detector. The second grating has a curved geometry as well and has a pitch different from the pitch of the first phase grating. According to another exemplary embodiment of the invention, the imaging apparatus further comprises a third grating which is an absorption grating positioned between the source and the object of interest and which also has a curved geometry. The third grating has a third pitch which is different from the first pitch of the phase grating and allows for an essentially coherent illumination of the phase grating.
According to another exemplary embodiment of the invention, the imaging apparatus further comprises a stepper motor. The beam of radiation emitted by the source has an optical axis, wherein the stepper motor is adapted for moving at least one of the phase grating and the second (absorption) grating along the optical axis of the beam of radiation emitted by the source.
Furthermore, the imaging apparatus may be adapted in such a way that the focal spot of the beam of radiation emitted by the source moves along the optical axis during image acquisition.
According to another exemplary embodiment of the invention, the imaging apparatus further comprises a rotating motor, wherein the rotating motor is adapted for rotating at least one of the phase grating and the second grating around the optical axis of the beam of radiation.
For example, the phase grating Gl and/or the second absorption grating G2 are adapted in spiral geometry and positioned on the optical axis. Alternatively or additionally, one or each of the two gratings Gl, G2 is positioned offset of the optical axis and rotated around the optical axis. According to another exemplary embodiment of the invention, the pitch of the phase grating (104) is not constant but a function of a distance from the center of the phase grating. In particular, the pitch may increase with increasing distance from the center. This may be also the case for the absorption gratings GO and G2. This may be useful to simplify the phase-stepping procedure along the optical axis.
According to another exemplary embodiment of the invention, the source is an X-ray source, wherein the apparatus is adapted as an X-ray based differential phase contrast imaging apparatus.
According to another exemplary embodiment of the invention, the source is a light source, wherein the imaging apparatus is adapted as an optical imaging apparatus where the beam of radiation used for probing the object is an optical radiation beam with a wavelength within the range of for example 400 to 1400 nm.
According to another exemplary embodiment of the invention, a method of phase-contrast imaging for examining an object of interest is provided, in which a beam of radiation is emitted by a source. Furthermore, a phase grating is positioned between the source and the detector. Phase stepping is performed along the optical axis with a focal spot, the phase grating and/or the absorber grating. Furthermore, radiation is detected by the detector after it has passed the object of interest and the phase grating, wherein the phase grating has a curved geometry.
According to another exemplary embodiment of the invention, a radial outward integration of the detected radiation is performed for phase retrieval. According to another exemplary embodiment of the invention, at least one of the phase grating, a second grating, which is an absorption grating positioned in front of the detector and having a curved geometry, and a focal spot of the beam of radiation emitted by the source is moved along an optical axis of the beam.
According to another exemplary embodiment of the invention, at least one of the phase grating, the second grating and the beam of radiation emitted by the source is rotated around an optical axis of the beam.
According to another exemplary embodiment of the invention, a computer-readable medium is provided, in which a computer program for examination of an object of interest is stored which, when executed by a processor of an imaging apparatus causes the imaging apparatus to carry out the above-mentioned method steps. According to another exemplary embodiment of the invention, a program element for examination of an object of interest is provided, which, when being executed by a processor of an imaging apparatus, causes the imaging apparatus to carry out the above-mentioned method steps.
It may be seen as a gist of the invention that three curved, for example circular or spiral- shaped gratings are used instead of three linear gratings for the DPC setup. In the case of linear gratings the phase stepping reveals the phase gradient along the Cartesian stepping direction. In the case of circular gratings aligned with the optical axis and thus respecting the cylindrical symmetry of the system, the phase stepping is performed along the optical axis with the focal spot, the phase grating or the absorber grating. The measured signal is the phase-gradient in the radial direction. The required positioning accuracy along the optical axis may be comparatively low compared to the relatively high accuracy required for the stepping in the case of linear gratings.
These and other aspects of the invention will become apparent from and elucidated with reference to the embodiments described hereinafter. Exemplary embodiments of the invention will be described in following, with reference to the following drawings.
BRIEF DESCRIPTION OF THE DRAWINGS Fig. IA shows a measurement setup with three linear gratings.
Fig. IB shows a cross-sectional view of the setup of Fig. IA. Fig. 2A shows a linear phase grating. Fig. 2B shows a linear absorption grating. Fig. 3 shows a measurement setup according to an exemplary embodiment of the invention.
Fig. 4 shows an imaging system according to an exemplary embodiment of the invention.
Fig. 5 shows a flow-chart of a method according to an exemplary embodiment of the invention.
DETAILED DESCRIPTION OF EMBODIMENTS The illustration in the drawings is schematically and not to scale. In different drawings, similar or identical elements are provided with the same reference numerals.
Fig. IA shows a measurement setup for differential phase-contrast imaging with linear gratings. An incoherent X-ray source is used which is symbolized by the focal spot 101. The radiation beam emitted by the source has an optical axis 4. First, the beam passes the absorption grating 1 (Go). Then, the beam passes the object of interest 103 and then the phase grating 2 (Gi). After that, the beam passes a second absorption grating 3 (G2), which is arranged before the imaging detector 102. Reference numeral 5 depicts the x-axis, reference numeral 6 the y-axis and reference numeral 7 the z-axis, which is arranged parallel to the optical axis 4.
Fig. IB shows a cross-sectional view of the setup depicted in Fig. IA. The focal spot of the source 101 has a width W, which is usually much bigger than the pitch po of the first absorption grating 1 (see reference numeral 8). The phase grating 2 is arranged a distance 1 from the first absorption grating 1. Between the first absorption grating 1 and the phase grating 2 is the object of interest 103.
The second absorption grating 3 is arranged a distance d from the phase grating 2, which has a pitch 10 (P2) which is smaller than the pitch of the first absorption grating 1. The phase grating 2 has a pitch 9 (pi) which allows that radiation from the source which has a certain energy E produces a Talbot image at the imaging detector 102.
Figs. 2A and 2B each show a section of the linear gratings 2 and 3, respectively.
Fig. 3 shows a filter and detector setup for an imaging apparatus according to an exemplary embodiment of the invention. The imaging setup has three circular gratings, i.e. an absorption grating 106 arranged after the focal spot of the source 101, a phase grating 104 arranged after the object of interest 103 and a second absorption grating 105 arranged before the detector 102.
The second absorption grating 105 can be moved or stepped along the optical axis 4. It should be noted, that the pitches of the circular (or spiral) gratings 104, 105 and 106 are not to scale. With respect to the system disclosed by Pfeiffer et al. all linear gratings are replaced by circular gratings (or spiral gratings) and the phase stepping is performed along the optical axis. The method is sensitive to the radial phase gradient.
The relation between the pitch pi of Gi and P2 of G2 remains unchanged. For a plane wave (synchrotron) p2=pl/2, for a spherical wave (as in the present case) p2=pl/2*l/(l-d), with 1 being the distance between GO and Gl and d the Talbot distance.
The source grating 106 is adapted to guarantee essentially ,,coherent" illumination of the phase grating 104. The distortions of the Talbot self-image (Fourier image) generated by the phase object 103 are analyzed by the absorption grating 105 through stepping along the optical axis 4. The detector measures the local phase- gradient in the radial direction. For phase-retrieval radial outward integrations are performed with the advantage of having a common "anchor" for the wave front phase.
According to another exemplary embodiment, the trenches of the gratings are not realized in the form of concentric rings but are realized as spirals. The phase stepping may then be implemented via a rotation of one of the gratings around the optical axis by an angle of 360 degrees.
It should be noted that a second phase grating (such as phase grating 410 of Fig. 4) may be positioned next to the first phase grating 104 in order to produce a second Talbot image at the detector. It should also be noted, that the imaging system may either be an X-ray imaging system or an optical imaging system.
Fig. 4 shows an imaging system 400 according to an exemplary embodiment of the invention. The imaging system depicted in Fig. 4 may be adapted in form of a mammography imaging system. The object of interest 103 may be a breast of a patient which is disposed between the two pressure plates 401, 402 for applying pressure to the patient's breast.
The source 101 may an X-ray source or, for instance, an optical energy source (in which case the system may be used for other purposes).
The radiation emitted by the source 101 first passes the grating 106 and then the object of interest to be imaged 103.
Then, the radiation passes a phase grating 104 and, if desired, a second phase grating 410. The phase gratings may be integrated in a corresponding housing and may thus form a module. The module is connected to the control unit 403 such that the gratings 104, 410 can be moved upwards and downwards along arrows 308, 309.
Furthermore, a second absorption grating 105 is positioned before the detector 102. Each of the gratings can be connected to the same or a respective individual motor 408 for moving the gratings along the arrows 308, 309 and/or for rotating the gratings around the optical axis 4.
Both the source 101 and the detector 102 are connected to the control unit 403 via lines 405, 406, respectively. The detector 102 comprises a Talbot interferometer 408.
Furthermore, a data line 407 connects the control unit 403 to an input and output device 404, which can be used for inputting control information for controlling the imaging system 400 and which can also be used for outputting visual information relating to the final image. Fig. 5 shows a flow-chart of a method according to an exemplary embodiment of the invention. In step 501 a beam of radiation is emitted by a source, for example an X-ray source emitting polychromatic x-rays. In step 502 focal spot, the phase grating or the absorption grating at the detector are stepped, i.e. moved along the optical axis. In case spiral gratings are used, a rotation is performed instead of the linear movement.
Then, in step 503 the radiation is detected after it has passed the object of interest and the gratings and in step 504 the phase is retrieved by performing radial outward integrations of the detected signal.
The integrations may also be started outside and heading inwards with a necessary condition to arrive at the same value on the optical axis.
It should be noted that the term "comprising" does not exclude other elements or steps and the "a" or "an" does not exclude a plurality. Also elements described in association with different embodiments may be combined.
It should also be noted that reference signs in the claims shall not be construed as limiting the scope of the claims. LIST OF REFERENCE SIGNS
1 Linear absorption grating
2 Linear phase grating
3 Linear absorption grating 4 Optical axis
5 x-axis
6 y-axis
7 z-axis
8 Pitch po 9 Pitch pi
10 Pitch p2
101 Source, focal spot
102 Detector
103 Obj ect of interest 104 Phase grating Gi
105 Absorption grating G2
106 Absorption grating Go
400 Imaging system
401 First pressure plate 402 Second pressure plate
403 Control unit
404 Input and output unit
405 Connection line
406 Connection line 407 Connection line
408 Motor
409 Rotating motor
410 Second phase grating
501, 502, 503, 504 Method steps

Claims

CLAIMS:
1. A phase contrast imaging apparatus for examining an object of interest, the apparatus (100) comprising: a source (101) for emitting a beam of radiation; a detector (102); a phase grating (104) positioned between the source (101) and the detector (102); wherein the detector (102) is adapted for detecting the radiation after it has passed the object of interest (103) and the phase grating (104); and wherein the phase grating (104) has a curved geometry.
2. Imaging apparatus of claim 1, wherein the phase grating has one of a circular geometry and a spiral geometry.
3. Imaging apparatus of one of claims 1 and 2, wherein the beam of radiation emitted by the source is a cone beam.
4. Imaging apparatus of one of claims 1 to 3, further comprising: a second grating (105); wherein the second grating (105) is an absorption grating positioned in front of the detector (102); wherein the second grating (105) has a curved geometry; and wherein the second grating (105) has a second pitch which is different from a first pitch of the phase grating (104).
5. Imaging apparatus of one of the preceding claims, further comprising: a third grating (106); wherein the third grating (106) ) is an absorption grating positioned between the source (101) and the object of interest (103); wherein the third grating (106) has a curved geometry; wherein the third grating (106) has a third pitch which is different from the first pitch of the phase grating (104) and allows for an essentially coherent illumination of the phase grating (104).
6. Imaging apparatus of one of the preceding claims, further comprising: a stepper motor (408); wherein the beam of radiation emitted by the source has an optical axis
(4); wherein the stepper motor (408) is adapted for moving at least one of the phase grating (104) and the second grating (105) along the optical axis of the beam of radiation emitted by the source.
7. Imaging apparatus of one of the preceding claims, further comprising: a rotating motor (409); wherein the beam of radiation emitted by the source has an optical axis
(4); wherein the rotating motor (409) is adapted for rotating at least one of the phase grating (104) and the second grating (105) around the optical axis of the beam of radiation emitted by the source.
8. Imaging apparatus of one of the preceding claims, wherein the source (101) is an x-ray source; and wherein the apparatus is adapted as an x-ray based differential phase contrast imaging apparatus.
9. Imaging apparatus of one of claims 1 to 7, adapted as an optical imaging apparatus; wherein the source (101) is a light source.
10. Imaging apparatus of one of the preceding claims, wherein the pitch of the phase grating (104) is a function of a distance from the center of the phase grating.
11. Method of phase contrast imaging for examining an object of interest, the method comprising the steps of: emitting a beam of radiation by a source; positioning a phase grating (104) between the source (101) and a detector (102); detecting, by the detector, the radiation after it has passed the object of interest (103) and the phase grating (104); wherein the phase grating (104) has a curved geometry.
12. Method of claim 11 , further comprising the step of: performing one of a radial outward integration and a radial inward integration of the detected radiation for phase retrieval.
13. Method of one of claims 11 or 12, further comprising the step of: rotating at least one of the phase grating (104), the second grating (105), and the beam of radiation emitted by the source around an optical axis of the beam.
14. A computer-readable medium, in which a computer program for examination of an object of interest is stored which, when executed by a processor of an imaging apparatus, causes the imaging apparatus to carry out the steps of: emitting a beam of radiation by a source; positioning a phase grating (104) between the source (101) and a detector (102); detecting, by the detector, the radiation after it has passed the object of interest (103) and the phase grating (104); wherein the phase grating (104) has a curved geometry.
15. A program element for examination of an object of interest, which, when being executed by a processor of an imaging apparatus, causes the imaging apparatus to carry out the steps of: emitting a beam of radiation by a source; positioning a phase grating (104) between the source (101) and a detector
(102); detecting, by the detector, the radiation after it has passed the object of interest (103) and the phase grating (104); wherein the phase grating (104) has a curved geometry.
PCT/IB2010/051098 2009-03-27 2010-03-15 Differential phase-contrast imaging with circular gratings WO2010109368A1 (en)

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