WO2014187588A1 - Système et procédé d'imagerie - Google Patents

Système et procédé d'imagerie Download PDF

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Publication number
WO2014187588A1
WO2014187588A1 PCT/EP2014/054151 EP2014054151W WO2014187588A1 WO 2014187588 A1 WO2014187588 A1 WO 2014187588A1 EP 2014054151 W EP2014054151 W EP 2014054151W WO 2014187588 A1 WO2014187588 A1 WO 2014187588A1
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WO
WIPO (PCT)
Prior art keywords
ray
imaging system
lenses
lens
lens array
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Application number
PCT/EP2014/054151
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German (de)
English (en)
Inventor
Oliver Heid
Original Assignee
Siemens Aktiengesellschaft
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Publication of WO2014187588A1 publication Critical patent/WO2014187588A1/fr

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Classifications

    • 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
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
    • 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
    • G—PHYSICS
    • G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
    • G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
    • G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
    • G21K1/06—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diffraction, refraction or reflection, e.g. monochromators
    • G21K1/065—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diffraction, refraction or reflection, e.g. monochromators using refraction, e.g. Tomie lenses
    • 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
    • A61B6/08—Auxiliary means for directing the radiation beam to a particular spot, e.g. using light beams
    • 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
    • A61B6/12—Arrangements for detecting or locating foreign bodies
    • 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

  • Imaging system and method for imaging The present invention relates to an imaging system comprising an X-ray source for emitting X-radiation, an imaging area and an X-ray detector. Furthermore, the invention relates to a method for imaging with such a system.
  • the attenuation of the intensity of the X-ray radiation is typically measured by the matter of an object to be examined, for example a human body part.
  • the absorption and the scattering of the X-radiation in the object to be examined thereby causes a weakening of the radiation incident on the detector, which depends on the mass, the atomic number and the irradiated material volume.
  • image attenuation of the mass attenuation varying over different positions of the object is then obtained.
  • Absorption imaging can be displayed very well.
  • a major challenge is the achievement of high soft tissue contrast in order to map diagnostic differences between different types of weakly absorbent tissue.
  • the method of the Phase-contrast imaging developed with X-ray light.
  • the spatially variable refractive index for X-radiation in the phase contrast X-ray instead of the absorption coefficients, the spatially variable refractive index for X-radiation in
  • a Talbot-Lau interferometer is used for this purpose, in which a plurality of very fine gratings are arranged partly before and partly behind the object to be examined and are displaced against each other in a plurality of successively performed measurements.
  • good contrasts are achieved with weakly absorbing tissue structures, since the refractive index for X-radiation is determined much more than the absorption coefficient of the concentration of light atoms such as carbon, oxygen and nitrogen.
  • the known method is very expensive in terms of apparatus, especially due to the production and positioning of the fine X-ray gratings, which require lattice constants in the range of 2 ⁇ .
  • the imaging system comprises an X-ray source for emitting X-radiation along a central beam axis, an imaging area for positioning an object to be examined and an X-ray detector.
  • a lens array of a plurality of X-ray focusing X-ray lenses is arranged.
  • the central beam axis is expediently aligned so that the object to be examined is transilluminated by the X-ray radiation emitted by the X-ray source.
  • the X-ray source expediently the smallest possible focal spot, so a small starting point for the emergence of X-rays, which advantageously has an effective diameter of at most 500 ⁇ , particularly advantageously at most 200 ⁇ . Due to the small extent of the focal spot, each subarea of the object volume is irradiated by X-ray radiation, which has only a small angular distribution within this area.
  • the imaging system according to the invention is suitable for this distortion of the wavefront with a
  • the X-ray detector is advantageously arranged so that the most complete possible angular range of the radiation without scattering the radiation hits the detector.
  • a lens field of x-ray lenses is arranged between the imaging area and the x-ray detector, ie between object and x-ray detector during operation of the imaging system.
  • the X-ray lenses have a focusing effect for X-ray radiation, whereby the radiation is concentrated in the direction of a plurality of focal points. For each X-ray lens, a focus location results.
  • the detection of the wavefront distortion works on the same principle as the measurement of an optical wavefront with a so-called Shack-Hartmann sensor. With an undistorted wavefront, the lens array focuses the incoming radiation onto a plurality of ideals
  • Focus places In the case of a distorted wavefront, on the other hand, the radiation is focused onto a plurality of focus locations which are more or less displaced relative to these ideal focus locations.
  • the X-ray detector is now expediently arranged and configured such that it can measure the displacement of the focus locations and thus the distortion of the radiation wavefront.
  • Particularly suitable is the imaging system described for use in medical diagnostics, especially in medical applications where a high
  • Soft tissue contrast is diagnostically relevant.
  • mammography in which the female breast is examined for very small tissue changes for the early detection and therapy-accompanying examination of breast cancer.
  • the contrast achievable solely by absorption is relatively low in this tissue, at least for medium-hard and harder X-rays. Therefore, mammography is an ideal field of application for phase-contrast imaging, where the distortion of the wavefront by low-absorbing tissue can also lead to a good image contrast.
  • the object to be positioned in the imaging area can alternatively also be another human or animal body part.
  • inanimate objects can also be investigated in the field of safety technology or industrial X-ray examinations.
  • an imaging system according to the invention is used to measure with the aid of X-ray radiation an aberration of the wavefront of the X-ray radiation caused by an object with the aid of the X-ray detector.
  • the advantages of the method according to the invention are analogous to the above-described advantages of the imaging system according to the invention.
  • Advantageous embodiments and further developments of the imaging system according to the invention will become apparent from the dependent claims of claim 1. Accordingly, the imaging system may additionally have the following features:
  • the lens array may be a two-dimensional array with a regular array of x-ray lenses.
  • a regular two-dimensional lens array results in a two-dimensional array of focus locations for the x-ray beam collimated by the lenses, which can be conveniently detected with a two-dimensional imaging x-ray detector.
  • the distortion of the wavefront occurring for different beam positions in the object can be measured in a simple manner.
  • a distortion value can thus be determined by the detector which, for the respective local beam direction between the focal spot and the respective lens, corresponds to the integral of the refractive index through the object along this direction.
  • the actual considered width of the volume area over which integration takes place is given by the spatial density of the lens field.
  • the density of the two-dimensional lens array thus determines the spatial resolution of the two-dimensional image information obtained for the object for a specific projection direction predetermined by the beam direction.
  • a regular arrangement of the x-ray lenses then leads to an image composed of regular picture elements.
  • the lens field may extend in at least one spatial direction perpendicular to the central beam axis. This ensures that the imaging system provides an image containing spatially resolved information with at least one spatial component that is perpendicular to the direction of projection.
  • a two-dimensional lens array may expediently extend in two spatial directions which are perpendicular to the central beam axis.
  • the lens array may comprise a plurality of single lens arrays stacked one behind the other along the central beam axis. This is useful when using a single
  • X-ray lens can not be achieved for a given beam arrangement desired focal length. Since the refractive index of most X-ray materials is very low In order to achieve a desired focus distance, it may be necessary to connect a plurality of lenses in the direction of the beam axis one behind the other for each projection direction to be imaged. For example, between 2 and 20 individual lens fields may be stacked along the beam axis.
  • At least a part of the x-ray lenses of the lens field can have a concave cross section on at least one side and in at least one sectional plane.
  • Concave X-ray lenses are useful because the refractive index of all materials is slightly below 1.
  • concentric focusing lenses can be produced with concave shapes.
  • the x-ray lenses may, for example, be biconcave or planar-concave. They can be designed, for example, as planar-concave cylindrical lenses, so that a concave cross-section results only in a sectional plane. In the other section plane containing the direction of the beam axis, such a cylindrical lens has, for example, a rectangular cross-section.
  • the lenses may also have a concave cross-section in all the sectional planes that comprise the direction of the beam axis.
  • the lenses can be embodied as planar-concave or biconcave lenses which are rotationally symmetrical about the direction of the beam axis and / or the local beam direction.
  • the lenses can each have an axis of symmetry which is aligned either for all lenses along the central beam axis or which is aligned for each lens along a local beam direction of the X-ray radiation.
  • the axes of symmetry of all the X-ray lenses of the lens array are expediently aligned substantially with the focal spot of the X-ray source.
  • the concave cross sections of the x-ray lenses can be shaped as spherical cross sections or as aspherical cross sections.
  • a particularly advantageous aspherical form is the parabolic shape with which for a parabolic cylindrical lens a line focus can be achieved and for a rotation-parabolic lens a point focus can be achieved.
  • At least a part of the x-ray lenses of the lens field can be configured as Fresnel lenses and / or as prism lenses.
  • Fresnel lenses are stepped molded lenses in which the cross section has, for example, a plurality of stepped concave portions instead of a simple concave shape.
  • a lens with comparable refractive effect can be constructed with a smaller volume of material.
  • this can significantly increase the transmission of the lens, since the ratio of refractive index decrement to the absorption coefficient for X-radiation is relatively poor for most materials.
  • Prism lenses also have the analog advantage of a relatively high refraction of light with low volume of material to be penetrated.
  • At least a portion of the x-ray lenses of the lens array may have a substantially point-shaped focus. If, for each transillumination direction to be imaged, at least one
  • Lens or a stack of lenses with common point-shaped focus is provided, then the object can be imaged as a distorted pattern of focus points, which are expediently focused in a common plane.
  • the displacements of the focus points can then be measured from the locations of the ideal focus points present at an undistorted wavefront.
  • at least a part of the x-ray lenses of the lens field may have a substantially line-shaped focus.
  • the lens field then expediently has a plurality of first x-ray lenses with a substantially linear focus, followed by a second x-ray lens having a substantially linear focus, the line focus of which is aligned essentially perpendicular to the line focus of the first x-ray lens.
  • a pair of single-lens fields can be With a line focus perpendicular to one another, a total lens angle with effective point focus can be generated. It is also possible for several such pairs to be arranged one after the other in the beam direction with mutually perpendicular line focus directions. The advantages of such arrangements are analogous to the x-ray lenses with a substantially point-shaped focus.
  • the x-ray lenses of the lens array may comprise a material whose average atomic number is at most 30.
  • the x-ray lenses of the lens array comprise a material whose average atomic number is at most 15.
  • Such rather lightweight materials are particularly suitable for forming x-ray lenses, since they have a particularly high ratio of refractive index decrement to absorption coefficient. It depends on the average atomic number, so that individual heavier elements can be present in a lower concentration.
  • Particularly suitable are materials comprising the elements beryllium, silicon, carbon, aluminum and / or nickel.
  • carbon-containing organic compounds can be used as lens material, for example, photolithographically structurable coatings such as SU-8 or polyimides, which can be structured with a precision in the submicrometer range.
  • silicon can be structured by lithographic methods.
  • films of beryllium, aluminum and / or organic compounds can be embossed, for example, with parabolically shaped needles, or the so-called LiGA process can be used to achieve high precision with the process steps lithography, electroplating and impression taking
  • the focal length of the x-ray lenses of the lens array can be up to 1 m.
  • the respectively favorable focal length also depends on the other geometric requirements of the imaging system, in particular on the size of the object to be examined.
  • the focal length of the x-ray lenses can advantageously be below 50 cm. It is also possible that the focal length of the x-ray lenses varies within the lens field. This can be advantageous since in arrangements with a planar lens field and a planar X-ray detector there are slight path length differences for the different local beam directions, so that a substantially sharp focus within the detector plane can be achieved with slightly varying focal lengths adapted to these differences.
  • the distance between the X-ray source and the lens field can be at least as large as the focal length of the X-ray lenses. Then, the distance between the X-ray detector and the lens field can also be selected such that the focal spot of the X-ray source is imaged substantially sharply in the plane of the X-ray detector by the X-ray lenses. With such an arrangement, a particularly high spatial resolution for the individual projection directions imaged by the x-ray lenses is obtained by the object.
  • the position of the X-ray detector may also be slightly in front of or behind the focal distance of the lens field. In such an embodiment, the X-ray radiation is not exactly focused but is distributed over a somewhat larger area of the detector surface. Such an arrangement may enable the measurement of the shift of focus locations with a relatively low spatial resolution of the X-ray detector.
  • the X-ray detector may comprise a plurality of detector elements, the number of which is at least as large as the number of X-ray lenses.
  • the detector elements are arranged in a regular pattern.
  • the X-ray detector expediently likewise comprises a two-dimensional arrangement of detector elements, wherein advantageously each of the two spatial directions of the detector is at least as large as the number of X-ray lenses in this spatial direction.
  • the number the detector elements in each spatial direction at least twice as large as the number of x-ray lenses. Then, for each of the x-ray lenses, at least one approximation value for the shift of the focus location can be determined by the distortion of the wavefront.
  • the spatial resolution of the imaging system is determined by the number of x-ray lenses, provided that the x-ray detector is high-resolution enough to determine the shift of the focus location for each of the x-ray lenses.
  • the contrast of the determination of the phase information and thus the image quality is essentially determined by the accuracy of the determination of these individual shifts.
  • the regular pattern of the detector elements may expediently extend in at least one spatial direction perpendicular to the central beam direction.
  • the regular pattern of the detector elements can be any regular pattern of the detector elements.
  • X-ray radiation deviate from the spatial arrangement of the x-ray lenses.
  • the advantage of such intentional mismatching of the two patterns with each other is that even with a small number of detector elements, the resulting radiation pattern can be scanned sufficiently to enable a determination of the displacements of the focus locations.
  • Fig. 1 is a schematic cross section of an imaging
  • Fig. 2 is a schematic cross section of the same imaging
  • System with an object to be examined shows 3 shows a schematic cross section of the lens array of the first embodiment
  • Fig. 5 is a schematic cross section of a lens array
  • FIG. 6 shows a schematic cross section of the X-ray detector of the first exemplary embodiment in a detailed view.
  • Fig. 1 shows a schematic cross section of a first embodiment of an imaging system 1 according to the present invention. Shown is the beam path of the X-radiation 5 from the X-ray source 3 through the imaging area 11 and the lens array 15 towards the X-ray detector 13. In FIG. 1, the imaging area 11 is still free of an object to be examined. The X-radiation 5 propagates from the focal spot 7 of the X-ray source 3 essentially undisturbed in the direction of the lens field 15. Therefore, the wavefront 27 of the X-ray radiation 5 is substantially undistorted shortly before entering the lens array 15.
  • the lens array 15 of the first exemplary embodiment is a regular arrangement of planar-concave X-ray lenses 17.
  • FIG. 1 schematically shows a cross section through four identical lenses 17.
  • each spatial direction of the two-dimensional lens array 15 can be arranged over a length of 10 cm about 500 to 2500 lenses. That is, the spatial period length of the lens array 15 may be in a uniform and equidistant arrangement, for example, between 200 ⁇ and 40 ⁇ .
  • the dimensions of the lens array 15 may be more in each spatial direction 10 cm, in mammography, for example, they can be about 25 cm by 30 cm.
  • the x-ray lenses 17 of the lens array 15 have a uniform focal length 21 of 25 cm.
  • focal length 21 may also assume other values that depend on the size of the object and geometric requirements for the placement of the object.
  • the focal length 21 may be in the range between 25 cm and 1 m.
  • the x-ray lenses 17 of the lens array 15 are formed as punctiform focusing parabolic lenses.
  • the x-ray radiation 5 is focused by each x-ray lens 17 in an associated focal point 19 both in the sectional plane of FIG. 1 and in the plane perpendicular thereto.
  • the distances of the individual components are selected such that the focal points 19 lie substantially on the image plane 31 of the two-dimensionally extended X-ray detector 13. This is achieved by the fact that the object distance is 23 and the image 25 the relation
  • the object width 23 is given as the distance between the focal spot 7 of the X-ray source 3 and the lens field 15
  • the image width 25 is given as the distance between the lens field 15 and the image plane 31 of the X-ray detector.
  • the undistorted wavefront 27 bundles the X-ray radiation onto a pattern of undisplaced, ideal focus points 19, the position of which can be imaged by the X-ray detector 13.
  • FIG. 2 shows a corresponding schematic cross section of the same imaging system 1 with an object 12 to be examined in the imaging area 11.
  • the imaging system 1 may additionally comprise an arrangement, not shown here, for holding an object 12 to be examined. This may be, for example, a patent bed or a device for receiving a body part.
  • the holder typically consists of two plates for fixation and compression of the female breast.
  • the X-ray radiation 5 When passing through the object 12 to be examined, the X-ray radiation 5 is weakened by absorption in its amplitude, as well as changed by refractive index differences in the spatial position of its wavefront 27. After passing through the object 12 thus results in a slightly distorted wavefront 27 ⁇ , which then passes through the lens array 15.
  • the distortion of the wavefront 27 ' causes a bundling of the X-ray radiation 5 in slightly shifted focal points 19 ⁇ , wherein the direction and the extent of the shift is characteristic of the displacement of the wavefront 27' in the respective irradiated volume region of the object 12.
  • X-ray lens 17 an effective wavefront shift for the associated volume element can be determined.
  • such an irradiated volume region 28i for an outer lens of the lens field 15 is characterized by hatching.
  • the number of x-ray lenses 17 decisively determines the spatial resolution of the entire imaging system 1.
  • FIG. 3 shows a schematic cross section of a detail view of the lens field 15 in the imaging system 1 of the first exemplary embodiment. Shown is a section in the region of the central beam axis 9.
  • all the x-ray lenses 17 are rotationally symmetrical about the direction of this central beam axis 9. Furthermore, all the x-ray lenses 17 lie in a plane which is perpendicular to this central beam axis 9.
  • the lens array 15 shows an alternative embodiment of the lens array 15 according to a second exemplary embodiment of the imaging system 1.
  • the individual x-ray lenses 17 are designed such that the axes of symmetry of the individual lenses 17 correspond to the respective local beam directions 29 of the x-ray radiation 5.
  • the Rotationsparaboloide the lens surfaces are thus slightly tilted against each other, so the individual lenses are aligned in the direction of the focal spot 7 of the X-ray source 3.
  • This somewhat more complex geometry has the advantage that the lens field 15 thus formed effects a sharper image of the focal spot 7 in the image plane 31 of the detector 13.
  • the object width 21 to be used in the imaging system 1 must already be determined.
  • both the lens field 15 and the X-ray detector 13 are each arranged on a flat surface.
  • the lens array 15 and / or the X-ray detector 13 are arranged on a curved surface, whereby a uniformly sharp image of the focal spot 7 on the detector surface 31 can also be achieved.
  • Fig. 5 shows an alternative embodiment of the lens array
  • the lens array 15 comprises a plurality of individual lens fields 16, each of which again has a two-dimensional, uniform arrangement of paraboloidal paraboloid.
  • the single-lens fields 16 are formed as fields of bi-concave x-ray lenses 17.
  • the advantage of the arrangement shown is that even with weak refractive lens materials focal lengths 21 can be achieved below 1 m. To achieve a given focal length 21, for example, up to 20 or even up to 100 individual lens fields
  • the material of the lens fields 15 is a lithographically patternable polyimide.
  • suitable alternative materials which preferably have an average atomic number of at most 15 and which have a high ratio of refractive index decrement to extinction coefficients.
  • 6 shows a schematic cross section of a detailed view of the X-ray detector 13 in the imaging system 1 of the first exemplary embodiment.
  • the X-ray detector 13 comprises a multiplicity of detector elements 33, which are arranged within an image plane 31 and absorb the X-ray radiation and in each case convert it into an electrical signal.
  • the X-ray detector 13 can either be designed as a direct converter in which the absorption takes place in a semiconducting material which directly generates an electrical signal. Examples of such materials are selenium or cadmium telluride. Or the detector 13 may alternatively comprise a field of photodiodes preceded by a scintillator or a plurality of scintillators each converting the x-radiation to visible light. Suitable scintillator materials are, for example, casium iodide or gadolinium oxysulfide. All these different embodiments have in common that the individual detector elements 33 are arranged so that they allow the measurement of the deflection of the focus points 19 'from the ideal focus positions 19'.
  • the X-ray detector 13 comprises a two-dimensional arrangement of detector elements 33, wherein in each spatial direction of the image plane, the number of detector elements 33 is twice as high as the number of X-ray lenses 17 of the lens array 15.
  • the X-radiation 5 is the spatial period length of the arrangement of the detector elements 33 expediently slightly larger than half the spatial period length of the lens array 15th
  • the detector elements 33 are arranged so that the ideal, unshifted focus points 19 each lie at the boundary of two detector elements 33.

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Abstract

Système d'imagerie comprenant une source de rayons X destinée à émettre des rayons X le long d'un axe de rayonnement central, une zone d'imagerie pour positionner un objet à analyser et un détecteur de rayons X. Entre la zone d'imagerie et le détecteur de rayons X est disposé un champs de lentilles composé d'une pluralité de lentilles à rayons X focalisant les rayons X. L'invention concerne en outre un procédé selon lequel un système d'imagerie selon l'invention est utilisé pour mesurer, au moyen du détecteur de rayons X et des rayons X, une distorsion du front d'onde des rayons X provoquée par un objet.
PCT/EP2014/054151 2013-05-22 2014-03-04 Système et procédé d'imagerie WO2014187588A1 (fr)

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DE102013209398.5A DE102013209398A1 (de) 2013-05-22 2013-05-22 Bildgebendes System und Verfahren zur Bildgebung
DE102013209398.5 2013-05-22

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WO2020214073A1 (fr) * 2019-04-18 2020-10-22 Prismatic Sensors Ab Optique de focalisation de rayons x en ligne utilisée dans la manipulation de rayons x dans une radiographie de transmission médicale
US11033243B2 (en) 2019-04-18 2021-06-15 Prismatic Sensors Ab In-line x-ray focusing optics used for manipulation of x-rays in medical transmission radiography
JP2022529923A (ja) * 2019-04-18 2022-06-27 プリズマティック、センサーズ、アクチボラグ 医療用透過ｘ線撮影におけるｘ線の操作に使用されるインラインｘ線集束光学系
JP7225432B2 (ja) 2019-04-18 2023-02-20 プリズマティック、センサーズ、アクチボラグ 医療用透過ｘ線撮影におけるｘ線の操作に使用されるインラインｘ線集束光学系

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