WO2011070488A1 - Imagerie par contraste de phase - Google Patents

Imagerie par contraste de phase Download PDF

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Publication number
WO2011070488A1
WO2011070488A1 PCT/IB2010/055561 IB2010055561W WO2011070488A1 WO 2011070488 A1 WO2011070488 A1 WO 2011070488A1 IB 2010055561 W IB2010055561 W IB 2010055561W WO 2011070488 A1 WO2011070488 A1 WO 2011070488A1
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WIPO (PCT)
Prior art keywords
grating
ray beam
grating arrangement
source
arrangement
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PCT/IB2010/055561
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English (en)
Inventor
Diester Geller
Klaus J. Engel
Gereon Vogtmeier
Thomas Koehler
Ewald Roessl
Original Assignee
Koninklijke Philips Electronics N.V.
Philips Intellectual Property & Standards Gmbh
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Application filed by Koninklijke Philips Electronics N.V., Philips Intellectual Property & Standards Gmbh filed Critical Koninklijke Philips Electronics N.V.
Priority to EP10798398.3A priority Critical patent/EP2509501B1/fr
Priority to CN201080063450.5A priority patent/CN102781327B/zh
Priority to RU2012128789/28A priority patent/RU2545319C2/ru
Priority to US13/514,682 priority patent/US9084528B2/en
Publication of WO2011070488A1 publication Critical patent/WO2011070488A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with 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 for radiation diagnosis, e.g. 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 for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
    • A61B6/4435—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being coupled by a rigid structure
    • A61B6/4441—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being coupled by a rigid structure the rigid structure being a C-arm or U-arm

Definitions

  • the invention relates to differential phase contrast imaging (PCI).
  • PCI differential phase contrast imaging
  • the invention relates to a device and method for differential phase contrast imaging.
  • the traditional X-ray systems used for medical applications are mainly based on the different absorption of X-rays in matter resulting in projection images formed by the accumulated absorption of the X-rays along a line. Yet, matter does not only influence the absorption but also the refraction of X-rays. This characteristics promises higher X-ray contrast between human tissue types than the conventional absorption-based imaging and hence can represent a future improvement.
  • a possible setup for facilitating PCI is based on gratings.
  • gratings within the transmitted X-ray beam face the problem, that non-focused gratings produce a less modulated absorption by themselves especially outside of the central region of the field-of-view (FOV), resulting in a decreased visibility of an interference pattern, a decreased transmitted mean intensity, and thus a lower signal-to-noise ratio at a detector. Therefore, the absorption image has either lower contrast-to-noise ratio or the radiation dose must be increased which the human body is potentially harmfully exposed. For the same reason, a typically non-focused source grating limits the FOV which can be exploited effectively by the PCI system.
  • This last aspect is caused by both the thickness of the source grating necessary for producing a minimal absorption for the X-rays and the slit width needed to filter out sufficiently coherent beams. All that leads to a decreased mean X-ray intensity and a decreased visibility of the interference pattern for locations in the resulting image outside the centre of the FOV.
  • a problem of differential phase contrast CT is that wrapping of the phase gradient occurs at the rim of the object. Different methods to unwrap the phase gradient have been proposed already, improving overall image quality substantially, but nevertheless, none of them works perfectly. Another approach is to avoid the phase wrapping by means of additional hardware.
  • a further drawback of differential phase contrast CT is the fact that the noise power spectrum of the image has a peak for low frequencies. The problem here is that low- frequency noise is perceived more annoying than high frequency noise.
  • the invention targets in improving an X-ray system based on phase contrast imaging (PCI).
  • PCI phase contrast imaging
  • a physician may be enabled to target the limited field of view (FOV) of a PCI system to a desired location.
  • This location may be selected with the help of a previous pure absorption scan with a large FOV by moving the grating arrangement out of the X-ray beam.
  • This previous scan can be performed with a lower intensity compared to conventional absorption-based scanning thus reducing the X-ray dose exposure to the object to scan.
  • a device for phase contrast imaging of an object comprises a source for an X-ray beam, a detector for detecting the X-ray beam, a grating arrangement, and a processing unit for controlling the phase contrast imaging, wherein the grating arrangement is movable out of the X-ray beam.
  • a device for phase contrast imaging of an object comprises a source for an X-ray beam, a detector for detecting the X-ray beam, a grating arrangement, and a processing unit for controlling the phase contrast imaging, wherein the processing unit is adapted to perform a local tomography.
  • Object' in the context of the invention may refer to a dead or living human or animal body or to a plant or portion of a plant. Furthermore, it may stand for an artificial part like a machine part or an assembly of parts, wherein these parts may be made out of one or more materials like metal, ceramic or plastic materials.
  • the device is capable of generating volumetric images of the object. That is, the device may be based, for example, on a source-detector combination which is capable to rotate around the object, for 3D-X-ray imaging.
  • the source and the detector may be located on separate devices to allow also a movement of one of the source and detector.
  • the source and detector may be fixed wherein the object will be located on a rotatable carrier.
  • the grating arrangement may include a source grating GO, a diffracting grating Gl and an analyzer grating G2, wherein the source grating is located between the source and the object, and wherein the diffracting grating and the analyzer grating are located between the object and the detector.
  • a PCI imaging without the source grating GO, i.e. only with the diffracting grating Gl and the analyzer grating G2.
  • the gratings of the grating arrangement may be mounted on one slider to facilitate the movement of the complete grating arrangement out of the X-ray beam.
  • the gratings GO, Gl and G2 may also be mounted on more than one slider so that also a separate or independent movement of the gratings may be realized.
  • the width of the grating arrangement is smaller than the width of the X-ray beam, so that a portion of the X-ray beam passes through the grating arrangement, when the grating arrangement is located within the X-ray beam.
  • the grating arrangement may be movable within the X-ray beam in a plane
  • the grating arrangement may be moved in the main direction of the X-ray beam to allow for a zoom of the PCI image.
  • the device according to the invention may comprise a variable aperture by means of which the width of the X-ray beam is adaptable to the width and the position of the grating arrangement.
  • the width of the grating arrangement may be substantially smaller than the width of the X-ray beam.
  • the variable aperture it is also possible to reduce the width of the X-ray beam so that the X-ray beam passes only the grating arrangement or even a sub-portion of the grating arrangement.
  • only a small portion of the object within the X-ray beam may be subjected to a radiation.
  • the possibility of moving or changing the position of the grating arrangement within the field of view of the X-ray beam provides for an appropriate positioning of the grating arrangement to a region of interest, and on the other hand for a reduction of radiation to which an object is subjected.
  • the device may further comprise a monitor for visualizing the position of the grating arrangement.
  • the device according to the invention may comprise an input device by means of which the position of the grating arrangement is controllable.
  • a user of the device may choose a region of interest in an X-ray image generated without a grating arrangement, and may shift a frame on the monitor to said region of interest, wherein the frame refers to the field of view through the grating arrangement.
  • the setup of a device for phase contrast imaging may be sketched as following:
  • the gratings GO, Gl, and G2 may be mounted on a movable slider whose movement may be controlled by a step motor that allows movements in the x,y-plane, i.e., perpendicular to the main direction of the X-ray beam path.
  • the step motors may be controlled by a software program that may be able to visualize the current position of the arrangement of gratings on a screen in a synchronous way.
  • the X-ray source may be mounted on a second slider that may be moved synchronously to the first slider but should be not activated when the first slider drives the gratings out of the X-ray path.
  • a method for phase contrast imaging of an object in accordance with a first embodiment comprises the step of moving a grating arrangement between a source for an X-ray beam, an object and a detector, so that a source grating of the grating arrangement is located between the source and the object, a diffracting grating and an analyzer grating of the grating arrangement are located between the object and the detector, and so that a portion of the X-ray beam passes through the grating arrangement.
  • another method for phase contrast imaging of an object comprises the steps of generating signals by means of a detector for detecting an X-ray beam, wherein a portion of the object is located together with a grating arrangement within the X-ray beam between a source for the X-ray beam and the detector, performing a local processing of the signals from the detector, and generating an image based on the processed signals, wherein the step of performing a local processing may include a qualitative assessment of adjacent detector pixels.
  • qualitative assessment may include a calculation of the first derivative of the signals by calculating the difference of the signal of two adjacent pixels of the detector array.
  • the local tomography aims in visualizing contours of internal structures of the object.
  • the proposed method enhances the possibility to tell the difference between structures, instead of presenting a representation of the quantitative measurements of each single detector pixel.
  • the method according to the second embodiment of the invention can even handle heavily truncated projection data and thus is well-suited for region of interest tomography.
  • the relative motion between the object and the system may be chosen such that the gratings are perpendicular to the projected source trajectory.
  • the step of performing a local processing may include a pixel-wise phase gradient retrieval and a calculating of a derivative of the phase gradient.
  • the generation of an image is performed using a weighted back-projection of the locally processed signals from the detector (D).
  • the method may further comprise the steps of generating an image of a portion of the object without the grating arrangement in the X-ray beam, and generating an image of a portion of the object with the grating arrangement within the X-ray beam, wherein the grating arrangement may be moved in a plane perpendicular to a main direction of the X-ray beam.
  • the method may further comprise the step of shifting at least one of the gratings for carrying out a phase stepping approach.
  • a common absorption-based image with a large FOV is produced.
  • This image is generated by driving the arrangement of the three gratings GO, Gl, and G2 that may be mounted on a movable slider out of the X-ray beam.
  • the setup thus delivers an image that is not deteriorated by the limitations of the gratings in any way and delivers an absorption image of the radiated body with no reduction of the FOV identical to common absorption imaging.
  • the grating arrangement is moved back, i.e., is inserted into the setup by, e.g., a step motor.
  • the position where the grating arrangement is inserted can be controlled.
  • the physician who performs the X-ray scan may be able to choose the exact position of the centre of this frame on the screen and can thus position that frame to a region-of-interest (ROI) that he is most interested in because the absorption image indicates a potential abnormality there.
  • ROI region-of-interest
  • the grating arrangement is synchronously inserted into the X-ray path to now produce a PCI image of this ROI.
  • the physician might decide to reduce the exposure in the first step if it is clear that the first step is only required to allow a positioning of the grating arrangement in the second step.
  • the directing of the FOV to a ROI results in a second advantage of the subject matter of the invention. From the absorption image that is more extended in size it is possible to roughly determine the predominant tissue type that can be expected within the ROI with the help of a list of absorption coefficients of for example typical human tissue types that the application is designed for. To this end also automatic segmentation algorithms applied online to the ROI may be helpful.
  • This information allows the optimization of the energy of the X-ray source for the following PCI scan together with the distance between Gl and G2— the Talbot distance— that are both related with the wavelength of the X-ray light. The optimization of the wavelength-related parameters may increases the quality of the resulting PCI image remarkably.
  • the Talbot distance may be modified in a similar way as done for the whole arrangement of the three gratings.
  • the invention can be used with any type of a PCI system where the FOV represents a limiting factor, for mammography, cardiac or head surgery systems, or computed tomography if the reconstruction is performed sufficiently fast so that the result can be visualized directly after the scan on a screen.
  • a computer program for phase contrast imaging is provided which, when executed on a processing unit of the device according to the invention, causing the device to perform the method according to the invention. Therefore, the method according to the invention may be performed substantially automatically, or at least predominantly automatically.
  • Such a computer program is preferably loaded into a work memory of a data processor.
  • the data processor is thus equipped to carry out the method of the invention.
  • the invention relates to a computer readable medium, such as a CD-ROM, at which the computer program may be stored.
  • the computer program may also be presented over a network like the World Wide Web and can be downloaded into the work memory of a data processor from such a network.
  • Fig. 1 is a schematically representation of a device for phase contrast imaging.
  • Fig. 2 illustrates an example of a field of view with a small region of interest.
  • Fig. 3 shows different tomography images.
  • Fig. 4 is a flowchart illustrating steps of a method according to the invention.
  • Figure 1 is a schematically representation of a grating setup for a Talbot-Lau type hard-X-ray imaging interferometer, which may be used in accordance with the invention.
  • the device will be described in the following in the context of a brief description of the functionality of the different parts of the device.
  • the hard-X-ray imaging interferometer comprises an incoherent X-ray source S, a source grating Go for achieving spatial beam coherence, a diffractive grating Gi (herein also referred to as phase grating) having a plurality of equidistant X-ray absorbing strips extending in parallel in a direction normal to the interferometer's optical axis, which serves as a phase-shifting beam splitter and is placed in downstream direction behind the object, an absorber grating G 2 (also referred to as analyzer grating) and an X-ray detector D for detecting the image data of a Moire interference pattern containing information about the phase shift of the deflected and phase-shifted X-ray beams after passing both the object O and the diffractive grating Gi
  • a processing means P of a workstation WS for recording the image data supplied by said radiation detector in a phase-stepping approach, a non- volatile read- access memory (RAM) for storing these data as well as a monitor screen MS or display for visualizing the recorded image data of the resulting Moire interference pattern are provided.
  • the source S the source is mounted on a first slider Sli
  • the detector D is mounted on a second slider Sl 2 .
  • two sliders it may be possible to move only one, the source or the detector, to generate for example a 2D image of a ROI of an object. Moving both, the source and the detector, simultaneously may lead to 3D imaging of the ROI.
  • the gratings may be arranged on a third slider SI 3 .
  • the whole grating arrangement may be easily moved out of the X-ray beam by means of for example a step motor SM.
  • the grating arrangement may be movable within the X-ray beam or out of the X-ray beam in a plane perpendicular to a main direction or optical axis OA of the X-ray beam. It will be understood that also separate sliders may be utilized for the different gratings (like for the source and detector).
  • the amount of the movement of the slider SI 3 to move the grating arrangement out of the X-ray beam may be at least one order greater than the amount of the movement of the grating G 2 within the X-ray beam induced by an actuator means AM to provide for the phase contrast imaging.
  • the movement of the slider may be a few mm or cm to position the grating arrangement within or outside the X-ray beam.
  • the movement of the absorber grating G 2 may be only a few ⁇ (micrometer).
  • the source grating Go creates an array of individually coherent, but mutually incoherent sources.
  • a structured source can be used, where the apertures of Go are replaced by spatially restricted emission areas of an X-ray source, which is for example represented by a structured anode in an X-ray tube.
  • the source grating can be even omitted if a micro-focus tube or a source with large spatial coherence, e.g., a synchrotron source is used.
  • Distributed X-ray sources with CNT based emitters alternatively could also form an array of coherent sources.
  • a phase object O in the beam path causes a slight refraction for each coherent subset of X-rays, which is proportional to the local phase gradient of the object. This small angular deviation results in changes of the locally transmitted intensity through the combination of gratings Gi and G 2 .
  • the phase grating Gi acts as a beam splitter and divides an incoming X-ray beam essentially into the two first diffraction orders. Since the wavelength ⁇ of the illuminating hard X-rays (which is typically in the order of below 0.1 nm) is much smaller than the grating pitch (which has a length of about 1 ⁇ ), the angle between two diffracted beams is very small. Downstream of the phase grating Gi, the diffracted beams interfere and form in certain distances known as fractional Talbot distances linear periodic fringe patterns with a periodicity g that equals half the phase grating times the geometric magnification factor defined by the distances GO to Gl and GO to G2.
  • the period and the lateral position of these fringes do not depend on the wavelength of the X-rays. Perturbations of the incident wave front, such as those induced by refraction on the object O in the beam, lead to local displacement of the fringes.
  • the imaging detector D placed in the detection plane may not have sufficient resolution to resolve the fringes. Therefore, the absorber grating G 2 , which has the same periodicity and orientation as the fringes, acts as a transmission mask for imaging detector D and transforms local fringe positions into signal intensity variations, and is placed immediately in front of the plane of the imaging detector D.
  • the detected signal profile hence contains quantitative information about the phase gradient ⁇ ( ⁇ , y)/dx of the object O.
  • phase-stepping approach may be adapted to this setup as well as a so-called blank scan, i.e., a scan without the object O.
  • the first one represents the intensity image that would have been received with no interferometer in the beam. It contains mainly absorption contrast and might also contain some in-line phase contrast caused by diffraction on the edges of the sample.
  • the intensity signal of the second image is proportional to the phase shift gradient in the object, which is why it is called the differential phase contrast image (DPCI).
  • DPCI differential phase contrast image
  • the DPCI can be used to obtain the phase profile of the object by a simple one-dimensional integration.
  • the quality of the gratings used in such an interferometer set-up is crucial.
  • micro-fabrication techniques are conventionally used. It is essential that the gratings Gi and G 2 have the correct ratio of periods. For a plane incoming wave, period /3 ⁇ 4 of absorber grating G 2 should be half of that of phase grating Gi, whereas for a cone-shape incoming wave, a slight correction needs to be included.
  • Micro lithography techniques need to be used to define the grating line pattern on silicon substrates.
  • phase grating Gi is characterized by low absorbing structures that introduce a phase shift ⁇ of about ⁇ radians to the passing X-ray waves
  • absorber grating G 2 is characterized by highly absorbing grating lines.
  • the actual size of the wave front's phase shift ⁇ after transmitting a line structure of phase grating Gi depends on the grating line thickness and on the wavelength ⁇ of the incident X-ray beam. If Gi is irradiated by a plane wave, a periodic interference pattern of intensity is formed in the detector plane that changes as a function of distance d between phase grating Gi and said detector plane.
  • a periodic pattern of linear fringes perpendicular to the grating lines is for example observed at the first fractional Talbot distance, which is given by d ⁇ / 8 ⁇ .
  • the pitch of these fringes equals half of the periodicity of the phase grating
  • phase grating Gi which is needed to obtain the required phase shift is proportional to the photon energy used and the phase shift coefficient of the grating material. For 17.5 keV and a grating material of silicon, a height of 22 um is an optimum.
  • phase grating Gi is close to 4 ⁇ resulting in very high aspect ratios of the structures.
  • the structures may be made by wet chemical etching in potassium hydroxide solution.
  • As substrates 250- ⁇ thick silicon wafers with (110) orientation are used.
  • the grating patterns are for example exposed using a high precision electron beam lithography process.
  • the orientation of the lines is along the (112) direction with a precision of better than 0.1°, which results in an anisotropic etching with vertical side walls.
  • the fabrication of the absorber grating G 2 is even more challenging.
  • the period /3 ⁇ 4 of the absorber grating has to be two times smaller than that of phase grating Gi, i.e., 2 um, and secondly, no simple etching process exists to pattern highly absorbing materials with high aspect ratios.
  • the structure height again depends on the photon energy and the absorption coefficient of the grating material At 17.5 keV, gold is used as an absorbing material.
  • a structure height of 10 um is desirable.
  • a silicon grating is patterned using the method described above. Then, the gaps of the grating are filled with gold by electro-deposition. Using a shadow evaporation process and selective wet etching, it is possible to let the gold grow from the bottom of the silicon grooves, as any deposition on the side walls or the silicon ridges would result in an incomplete filling of the grooves.
  • Differential phase contrast projection data of a region of interest are acquired over an angular range of preferentially at least 180 degrees.
  • Typical and preferred acquisition uses a circular path around the region of interest with a data acquisition over 360 degrees or 180 degrees plus the fan-angle of the detector.
  • data can be acquired using a helical path of the source detector arrangement around the region of interest. It is preferred that the direction of differentiation coincides with the tangent of the path of the X-ray source projected onto the detector.
  • the first derivative of these differential projection data is calculated numerically along the same direction (viz., the direction of the projected tangent to the source path).
  • pre-processed projection data are back-projected into the region of interest.
  • two weighting functions can be applied to improve the image quality.
  • the first one is a redundancy weighting function, which ensures that the contribution of redundant data sum up the reconstructed image in a normalized fashion.
  • this weighting function can be as simple as a constant factor of 1/2.
  • the second weighting that may be used is a density correction.
  • the density of rays is calculated, squared and used as an additional back-projection weight. If the fan-angle of the system is small, or the region of interest to be reconstructed fits into a small fan-angle, this density compensation can be discarded in order to simplify the back-projection operation.
  • the term "redundant" is used a little bit imprecisely in the area of cone-beam reconstruction.
  • the rotation axis is preferably aligned with the y-axis.
  • any two data acquired during the scan are considered to be "redundant" for an object point within the region of interest if, firstly, the object point is located somewhere on the ray from the source to the detector that corresponds to this detection value, and secondly, the rays, projected parallel to the y-axis onto the zy-plane coincide.
  • the cone-beam data may be rebinned into pseudo-parallel (aka wedge) geometry.
  • the density correction factor should not to be squared when used as back-projection weight.
  • a main idea of the invention is to apply the theory of local tomography to the problem of differential phase contrast CT.
  • the approach starting from the local tomography function is outlined.
  • the measurement provides line integrals for each source position, which is parameterized by a scalar variable s, and for each direction a (here and in the following, bold symbols relate to vectors):
  • the weighting function ⁇ takes care of redundancies. It is known that the local tomography function recovers local features of the object function/ and that remaining nonlocal artifacts are an order of magnitude smaller.
  • the derivative is taken along a different coordinate. Specifically, for a planar detector with coordinates u and v, where v is the direction of the gratings, the derivative is measured in the direction of u:
  • the w-direction should be aligned with the tangent to the source path y(s).
  • Figure 2 shows in the upper portion of the figure an exemplary absorption image generated without a grating arrangement, having a visible FOV. Further, there is illustrated a frame in the absorption image serving as a indication of a ROI, wherein the frame may be moved by command of an input device to a ROI.
  • the lower portion of figure 2 illustrates a PCI image of said ROI, wherein in this example the PCI image may be enlarged and visualized separately from the absorption image. It is noted that the PCI image may also be an overlay on the absorption image, for example in the frame, and may also be illustrated in the same scale as the absorption image.
  • Figures 3A, 3B, and 3C show exemplarily reconstruction results obtained by the proposed method.
  • the local tomography approach recovers local structures quite well.
  • the artifacts caused by the non-perfect phase unwrapping at the object boundary are also present only locally.
  • the image in figure 3C illustrates that the non- perfect phase unwrapping causes non-local artifacts in a conventional tomographic reconstruction of the differential data.
  • the flowchart in figure 4 illustrates the principle of the method for phase contrast imaging according to the invention. It will be understood that the steps described with respect to the method are major steps, wherein these major steps might be differentiated or divided into several sub-steps. Furthermore, there might be also sub-steps between these major steps. Therefore, a sub-step is only mentioned if that step is important for the understanding of the principles of the method according to the invention.
  • an X-ray scan may be performed with the arrangement of gratings driven out facilitating to produce a pure absorption image of the object in-between.
  • the absorption image may be visualized on a screen so that the user can evaluate it together with an overlay of the current position of the arrangement of gratings in form of a frame having the same size as the FOV that is covered by the arrangement of gratings within the X-ray path.
  • step S2 the user can move the frame via e.g. a computer mouse to a position within the absorption image he wants to do a PCI scan of a suspicious region.
  • the slider SI 3 of the grating arrangement and the sliders Sli and SI2 of the source may be moved to the indicated position so that the grating arrangement covers an area on the plane perpendicular to the main X-ray beam path, the same as the frame within the absorption image on the computer screen.
  • a PCI scan may be performed and visualized on the computer screen allowing the user to inspect it.
  • This PCI scan may include the advantages of the local tomography. If desired the PCI scan may be repeated in step S4 at other ROIs with the help of the same absorption image.
  • a computer program may be stored/distributed on a suitable medium such as an optical storage medium or a solid-state medium supplied together with or as a part of another hardware, but may also be distributed in other forms, such as via the internet or other wired or wireless telecommunication systems. Any reference signs in the claims should not be construed as limiting the scope.

Abstract

Les dispositifs de radiographie pour l'imagerie par contraste de phase sont souvent construits à l'aide de réseaux. De plus grands champs de vision impliquent une augmentation considérable du coût de production et de la complexité de ces réseaux, car ceux-ci nécessitent une géométrie focalisée. Au lieu d'une imagerie par contraste de phase pure à grand champ de vision, l'invention combine un système d'imagerie radiographique par absorption classique à grand champ de vision et un système d'imagerie par contraste de phase peu coûteux insérable à petit champ de vision. L'invention permet à l'utilisateur de diriger le système d'imagerie par contraste de phase présentant un champ de vision réduit vers une région qu'il estime être la plus intéressante pour mettre en œuvre un balayage d'imagerie par contraste de phase, ce qui permet de supprimer l'exposition à une dose de rayons X pour balayer des régions sans intérêt pour un radiologue. Le balayage d'imagerie par contraste de phase peut être produit sur la base d'une tomographie locale.
PCT/IB2010/055561 2009-12-10 2010-12-03 Imagerie par contraste de phase WO2011070488A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
EP10798398.3A EP2509501B1 (fr) 2009-12-10 2010-12-03 Imagerie par contraste de phase
CN201080063450.5A CN102781327B (zh) 2009-12-10 2010-12-03 相衬成像
RU2012128789/28A RU2545319C2 (ru) 2009-12-10 2010-12-03 Формирование фазово-контрастных изображений
US13/514,682 US9084528B2 (en) 2009-12-10 2010-12-03 Phase contrast imaging

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP09178701 2009-12-10
EP09178701.0 2009-12-10

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WO2011070488A1 true WO2011070488A1 (fr) 2011-06-16

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US (1) US9084528B2 (fr)
EP (1) EP2509501B1 (fr)
CN (1) CN102781327B (fr)
RU (1) RU2545319C2 (fr)
WO (1) WO2011070488A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2015044001A1 (fr) 2013-09-30 2015-04-02 Koninklijke Philips N.V. Dispositif d'imagerie à contraste de phase différentielle ayant un ou plusieurs réseaux mobiles
WO2017006620A1 (fr) * 2015-07-03 2017-01-12 コニカミノルタ株式会社 Interféromètre de talbot-lau

Families Citing this family (31)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN102221565B (zh) * 2010-04-19 2013-06-12 清华大学 X射线源光栅步进成像系统与成像方法
CN103189739B (zh) * 2010-10-19 2015-12-02 皇家飞利浦电子股份有限公司 微分相位对比成像
EP2630476B1 (fr) * 2010-10-19 2017-12-13 Koninklijke Philips N.V. Imagerie différentielle en contraste de phase
WO2012164092A1 (fr) * 2011-06-01 2012-12-06 Total Sa Dispositif de tomographie à rayons x
RU2585801C2 (ru) 2011-06-01 2016-06-10 Тоталь Са Устройство рентгеновской томографии
WO2013111050A1 (fr) * 2012-01-24 2013-08-01 Koninklijke Philips N.V. Imagerie par rayons x à contraste de phase multidirectionnelle
WO2014137325A1 (fr) * 2012-03-05 2014-09-12 University Of Rochester Procédés et appareils pour tdm à faisceau conique à contraste de phase différentiel et tdm à faisceau conique hybride
DE102012005767A1 (de) * 2012-03-25 2013-09-26 DüRR DENTAL AG Phasenkontrast-Röntgen-Tomographiegerät
CN104394770B (zh) 2012-06-27 2018-06-08 皇家飞利浦有限公司 基于光栅的差分相位对比成像
US9775575B2 (en) 2012-06-27 2017-10-03 Koninklijke Philips N.V. Dark-field imaging
US9839407B2 (en) * 2013-06-28 2017-12-12 Koninklijke Philips N.V. Correction in slit-scanning phase contrast imaging
CN104622492A (zh) * 2013-11-11 2015-05-20 中国科学技术大学 一种x射线光栅相位衬度成像装置和方法
JP2015213665A (ja) * 2014-05-12 2015-12-03 キヤノン株式会社 放射線撮像装置
EP3102109B1 (fr) 2014-06-16 2017-11-08 Koninklijke Philips N.V. Acquisition de données hybride de tomodensitométrie (tdm)
WO2016104008A1 (fr) * 2014-12-22 2016-06-30 株式会社島津製作所 Dispositif d'imagerie par contraste de phase de rayonnement
JP6451400B2 (ja) * 2015-02-26 2019-01-16 コニカミノルタ株式会社 画像処理システム及び画像処理装置
CN106153646B (zh) * 2015-04-08 2022-06-24 清华大学 X射线成像系统和方法
US11116465B2 (en) 2015-09-16 2021-09-14 Koninklijke Philips N.V. Dark-field enhanced virtual x-ray colonoscopy
RU2612322C1 (ru) * 2016-04-07 2017-03-07 Федеральное государственное бюджетное образовательное учреждение высшего образования "Рязанский государственный радиотехнический университет" (ФГБОУ ВО "РГРТУ") Способ развертывания фазы при интерферометрической обработке информации от космических систем радиолокационного наблюдения земли
CN105738387B (zh) * 2016-04-14 2018-10-23 苏州工业园区道青科技有限公司 轮毂检测用装置
US10660595B2 (en) * 2016-06-16 2020-05-26 Koninklijke Philips N.V. Apparatus for x-ray imaging an object
CN110049727B (zh) 2016-12-06 2023-12-12 皇家飞利浦有限公司 用于基于光栅的x射线成像的干涉仪光栅支撑物和/或用于其的支撑物托架
EP3551077A1 (fr) 2016-12-09 2019-10-16 Koninklijke Philips N.V. Appareil d'acquisition de données de projection et dispositif de support de sujet
EP3403581A1 (fr) 2017-05-15 2018-11-21 Koninklijke Philips N.V. Dispositif de montage de bâti pour imagerie à contraste de phase différentiel par balayage de fentes
US10441234B2 (en) * 2017-06-15 2019-10-15 Shimadzu Corporation Radiation-phase-contrast imaging device
CN107290846B (zh) * 2017-08-04 2019-06-21 南京理工大学 基于环状可编程led照明的定量相位显微成像方法
EP3450967A1 (fr) * 2017-09-01 2019-03-06 Shimadzu Corporation Appareil d'imagerie par rayons x
JP6838531B2 (ja) * 2017-09-06 2021-03-03 株式会社島津製作所 放射線位相差撮影装置
JP2019066283A (ja) 2017-09-29 2019-04-25 株式会社島津製作所 放射線位相差撮影装置
JP7069670B2 (ja) * 2017-12-04 2022-05-18 コニカミノルタ株式会社 Ｘ線撮影システム
CN112270741B (zh) * 2020-10-13 2024-04-09 南京大学 一种基于偏振的光栅相位衬度成像系统及方法

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040131145A1 (en) * 2002-12-27 2004-07-08 Konica Minolta Holdings, Inc. Mammography apparatus
US20070183559A1 (en) * 2006-02-01 2007-08-09 Eckhard Hempel X-ray CT system for producing projective and tomographic phase contrast images

Family Cites Families (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5745665A (en) * 1994-07-20 1998-04-28 Douglas F. Winnek Method for processing a three-dimensional data set into a composite two-dimensional image viewable as a three-dimensional image
DE69622406D1 (de) * 1995-04-28 2002-08-22 Forskningsct Riso Roskilde Phasenkontrastbilderzeugung
JPH09187455A (ja) * 1996-01-10 1997-07-22 Hitachi Ltd 位相型ｘ線ｃｔ装置
RU2115943C1 (ru) * 1997-01-16 1998-07-20 Виктор Натанович Ингал Способ фазовой рентгенографии объектов и устройство для его осуществления (варианты)
FI116750B (fi) * 2002-08-28 2006-02-15 Instrumentarium Corp Lääketieteellisen röntgenkuvauksen menetelmä ja järjestely
JP2005006772A (ja) * 2003-06-17 2005-01-13 Ge Medical Systems Global Technology Co Llc Ｘ線診断装置及びｃｔ画像の生成方法
US7260174B2 (en) * 2004-09-13 2007-08-21 General Electric Company Direct conversion energy discriminating CT detector with over-ranging correction
EP1731099A1 (fr) 2005-06-06 2006-12-13 Paul Scherrer Institut Interféromètre pour l'imagerie et la tomographie à contraste de phase avec une source de rayons X incohérente et polychromatique
DE102006015358B4 (de) * 2006-02-01 2019-08-22 Paul Scherer Institut Fokus/Detektor-System einer Röntgenapparatur zur Erzeugung von Phasenkontrastaufnahmen, zugehöriges Röntgen-System sowie Speichermedium und Verfahren zur Erzeugung tomographischer Aufnahmen
CN101011256A (zh) 2006-02-01 2007-08-08 西门子公司 通过x射线无破坏地分析检查对象的方法和测量装置
DE102006037282B4 (de) * 2006-02-01 2017-08-17 Siemens Healthcare Gmbh Fokus-Detektor-Anordnung mit röntgenoptischem Gitter zur Phasenkontrastmessung
US7609392B2 (en) * 2006-06-28 2009-10-27 California Institute Of Technology Harmonically matched diffraction grating pair
EP1879020A1 (fr) 2006-07-12 2008-01-16 Paul Scherrer Institut Interféromètre par rayons X pour l'imagerie à contraste de phase
US7920673B2 (en) * 2007-10-30 2011-04-05 Massachusetts Institute Of Technology Phase-contrast x-ray imaging
ATE524056T1 (de) * 2007-11-15 2011-09-15 Suisse Electronique Microtech Interferometervorrichtung und verfahren
CN101576515B (zh) * 2007-11-23 2012-07-04 同方威视技术股份有限公司 X射线光栅相衬成像系统及方法
CN102316791B (zh) 2009-02-12 2015-05-20 皇家飞利浦电子股份有限公司 用于边缘成像的接口装置、成像系统和方法
JP2010253194A (ja) * 2009-04-28 2010-11-11 Fujifilm Corp 放射線位相画像撮影装置
EP2442722B1 (fr) 2009-06-16 2017-03-29 Koninklijke Philips N.V. Procéde de correction pour imagerie de contraste de phase différentielle

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040131145A1 (en) * 2002-12-27 2004-07-08 Konica Minolta Holdings, Inc. Mammography apparatus
US20070183559A1 (en) * 2006-02-01 2007-08-09 Eckhard Hempel X-ray CT system for producing projective and tomographic phase contrast images

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
MARTIN BECH ET AL: "Soft-tissue phase-contrast tomography with an x-ray tube source; Soft-tissue phase-contrast tomography", PHYSICS IN MEDICINE AND BIOLOGY, TAYLOR AND FRANCIS LTD. LONDON, GB, vol. 54, no. 9, 7 May 2009 (2009-05-07), pages 2747 - 2753, XP020149963, ISSN: 0031-9155, DOI: DOI:10.1088/0031-9155/54/9/010 *
PFEIFFER F ET AL: "High-resolution brain tumor visualization using three-dimensional x-ray phase contrast tomography; High-resolution brain tumor visualization using x-ray phase contrast tomography", PHYSICS IN MEDICINE AND BIOLOGY, TAYLOR AND FRANCIS LTD. LONDON, GB, vol. 52, no. 23, 7 December 2007 (2007-12-07), pages 6923 - 6930, XP020127270, ISSN: 0031-9155 *

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2015044001A1 (fr) 2013-09-30 2015-04-02 Koninklijke Philips N.V. Dispositif d'imagerie à contraste de phase différentielle ayant un ou plusieurs réseaux mobiles
JP2016531659A (ja) * 2013-09-30 2016-10-13 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． 可動式格子を含む微分位相コントラスト撮像装置
US9649082B2 (en) 2013-09-30 2017-05-16 Koninklijke Philips N.V. Differential phase contrast imaging device with movable grating(s)
WO2017006620A1 (fr) * 2015-07-03 2017-01-12 コニカミノルタ株式会社 Interféromètre de talbot-lau

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