WO2009027904A2 - Système d'imagerie par rayons x avec un agencement cylindrique de source et de détecteur - Google Patents

Système d'imagerie par rayons x avec un agencement cylindrique de source et de détecteur Download PDF

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Publication number
WO2009027904A2
WO2009027904A2 PCT/IB2008/053353 IB2008053353W WO2009027904A2 WO 2009027904 A2 WO2009027904 A2 WO 2009027904A2 IB 2008053353 W IB2008053353 W IB 2008053353W WO 2009027904 A2 WO2009027904 A2 WO 2009027904A2
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WIPO (PCT)
Prior art keywords
ray
detector
source
imaging system
cone
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PCT/IB2008/053353
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English (en)
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WO2009027904A3 (fr
Inventor
Roland Proksa
Axel Thran
Michael Grass
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Koninklijke Philips Electronics N.V.
Philips Intellectual Property & Standards Gmbh
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Publication of WO2009027904A2 publication Critical patent/WO2009027904A2/fr
Publication of WO2009027904A3 publication Critical patent/WO2009027904A3/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
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4007—Arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
    • A61B6/4014—Arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units arranged in multiple source-detector units
    • 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
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4021—Arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot
    • A61B6/4028—Arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot resulting in acquisition of views from substantially different positions, e.g. EBCT
    • 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
    • A61B6/508—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 non-human patients
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1644—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using an array of optically separate scintillation elements permitting direct location of scintillations
    • 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
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/027—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral
    • 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
    • A61B6/503—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 the heart
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00—X-ray tubes

Definitions

  • the invention relates to an X-ray imaging system, to a method for controlling such an X-ray imaging system, to an associated program element, and to a computer-readable medium.
  • X-ray sources are known in many different designs and for many different purposes.
  • One important application is their use in (e.g. medical) X-ray imaging devices in which an object to be examined is exposed to X-rays from an X-ray source and wherein the transmitted radiation is detected.
  • CT Computerputed Tomography
  • the US 2002/0094064 Al describes a particular X-ray imaging system with a cylindrical X-ray source that comprises carbon nanotubes as cathodes for emitting electrons onto a X-ray emitting target.
  • a cylindrical X-ray detector is arranged - axially shifted with respect to the target - within the cylindrical X-ray source.
  • the invention relates to an X-ray imaging system, i.e. to a device or apparatus that uses X-rays to generate an image of an object.
  • the imaging process may particularly comprise the detection of X-rays that were transmitted through an object and thus provide information about the local absorption coefficients of the object.
  • the X-ray imaging system may especially be a rotational X-ray device, in which the focal spot of X-ray emission at least partially rotates around an object. In a Computed Tomography (CT) scanner, a sectional image through the object is thus reconstructed from X-ray projections of the object taken under different angles.
  • CT Computed Tomography
  • the X-ray imaging system comprises the following components:
  • the geometrical cone will be called “source cone” and the given axis will be called “system axis” in the following.
  • the "X-ray emitting components" of the X-ray source will usually comprise some target material like a heavy metal that emits X-rays when being bombarded with high-energy electrons.
  • Other components of the X-ray source for example associated electronic circuits, will usually be arranged at appropriate locations off the source cone.
  • the source cones of the first and second X-ray source may optionally be identical.
  • the aforementioned geometrical cone will be called "detector cone" in the following.
  • the "sensitive area" of the X-ray detector may be realized by an X-ray sensitive film; more preferably, it may comprise some converter material in which X-rays are (directly or indirectly) converted into electrical signals, e.g. photocurrents of photodiodes.
  • Other components of the X-ray detector, for example associated signal processing electronics, will usually be arranged at appropriate locations off the detector cone.
  • the invention relates to an X-ray imaging system comprising the following components:
  • imaging systems are closely related to each other; all remarks and explanations made with respect to the first imaging system therefore apply correspondingly also to the second imaging system.
  • Both imaging systems have in common an axial "sandwich structure" of X-ray emitting and X-ray detecting components, i.e. of the kind “source-detector-source” (first imaging system) or
  • the sandwich structure has the advantage to provide a more uniform, symmetrical irradiation and detection of the region within the detector/source cones. Moreover, a larger volume can simultaneously be X-rayed, thus increasing the information per exposure and decreasing the necessary examination time.
  • the X-ray source or sources that are comprised by the X-ray imaging system may optionally comprise at least one cathode with carbon nanotubes for emitting electrons that generate X-rays when being bombarded onto a target.
  • Carbon nanotubes have been shown to be excellent electron emitting materials which allow fast switching times with a compact design.
  • the at least one X-ray source of the X-ray imaging system comprises a plurality of focal spots from which
  • X-radiation can selectively be emitted.
  • the term "focal spot" shall denote the region within the X-ray source from which X-rays are or can be emitted during operation.
  • X-ray sources according to the state of the art usually have only one stationary focal spot.
  • the X-ray source proposed here preferably has a (large) number of focal spots which can selectively be activated to emit X-rays.
  • the X-ray emitting area of the X-ray source can be increased accordingly, wherein the focal spots may simultaneously or sequentially be activated. In the latter case, the location of X-ray emission can be moved in space without moving a physical component.
  • each focal spot has an associated cathode (particularly realized with carbon nanotubes) that provides it with electrons thus providing a simple way to generate X-rays at a large number of focal spots.
  • the X-ray source comprises a controller for a) selecting a set of voltages and associated focal spots, and b) applying said voltages to said focal spots according to a given temporal schedule.
  • the "application of a voltage to a focal spot” means that an associated electron emitting cathode is supplied with a negative potential and that the anode- material at the focal spot is supplied with to a positive potential with the potential difference corresponding to the acceleration voltage.
  • the anode material may also be at zero-potential.
  • the acceleration voltages correspond to the (possibly individual) negative potentials of the cathodes.
  • the application of voltages to focal spots may take place simultaneously, sequentially (i.e. there is only one voltage applied to an associated focal spot at a time while e.g. the electrical potential of the residual focal spots floats), or in a mixed way with arbitrary temporal overlaps between the application of voltages to focal spots.
  • the set of voltages may comprise an individual voltage for each focal spot or, alternatively, only a few (or just one) particular voltage values that are applied to a larger number of focal spots.
  • the controller comprises a digital data processing unit with an associated memory for storing program instructions.
  • the aforementioned controller preferably comprises a digital data processing unit, for example a microprocessor, with an associated memory (e.g. RAM, hard disc, etc.) for storing program instructions.
  • a digital data processing unit for example a microprocessor
  • an associated memory e.g. RAM, hard disc, etc.
  • both the X-ray source and the X-ray detector are arranged with respect to a source cone and a detector cone, respectively, that have a common axis (the "system axis").
  • the source cone and particularly the detector cone are cylinders.
  • the diameters of such a source cylinder and detector cylinder may be the same or preferably be different. In the latter case, regions within the cylinders that are shadowed from X-radiation due to housing components can be reduced to a minimum.
  • the at least one X-ray source is arranged stationary with respect to the at least one X-ray detector, wherein the X-ray detector has a sensitive area that is large enough to capture all X-rays which can effectively be emitted by the X-ray source (i.e. all generated X-rays that are not blocked by shutters, collimators, housing components or the like).
  • the last requirement is particularly relevant if there are several focal spots that can selectively be activated to emit X-ray beams, because then all effectively possible X-ray beams can reach the sensitive area without the necessity of moving the detector relative to the X-ray source.
  • the X-ray source and the detector can therefore be rigidly coupled, which makes the mechanical design easier and which guarantees maximal precision with respect to their mutual alignment.
  • the X-ray emitting components of the X-ray source may optionally cover an angle of at least 180°+ ⁇ on the associated source cone, wherein ⁇ is the fan angle of the X-ray source. In this case it is possible to irradiate an object in the cylinder from all sides, which is a necessary requirement for reconstructions with Computed Tomography.
  • the sensitive area of the X-ray detector covers an angle of at least 180°+ ⁇ on the associated detector cone, wherein ⁇ is again the fan angle of the X-ray source. If combined with the previous embodiment, a design can be achieved in which the X-ray detector can capture all X-ray beams that can be emitted by the X-ray source.
  • the X-ray source and/or the X-ray detector can be rotated about the system axis.
  • the angular extension of the X-ray source and/or the X-ray detector can be kept smaller than 180°+ ⁇ .
  • the X-ray emitting components of the X-ray source and the sensitive area of the X-ray detector may at least partially extend over a common section of the system axis. In this interval of axial overlap, the emitting components and the sensitive area preferably extend circumferentially over different angles to avoid a mutual shadowing.
  • the X-ray imaging system may further optionally comprise a carrier for carrying an object to be X-rayed. In a medical environment, the carrier may typically be a table on which a patient to be examined can rest. The material and construction of the carrier is preferably chosen in such a way that it has a minimal effect on generated X-ray images. According to a further development of the aforementioned embodiment, the
  • X-ray source and/or the X-ray detector on the one hand and the carrier on the other hand are designed such that they can axially be shifted with respect to each other. This particularly includes the cases that the X-ray source and the X-ray detector can commonly be shifted with respect to the carrier or vice versa.
  • the possibility of an axial shift can be exploited to eliminate shadow zones that are not reached by X-rays in an axially stationary arrangement. It should be noted that the relative shift of the X-ray source/detector and the carrier is usually automatically controlled and executed during a scan.
  • the invention further relates to a method for controlling an X-ray imaging system of the kind described above, said method comprising the emission of X-radiation from focal spots of the at least one X-ray source according to a given temporal and spatial schedule.
  • a method for controlling an X-ray imaging system of the kind described above comprising the emission of X-radiation from focal spots of the at least one X-ray source according to a given temporal and spatial schedule.
  • a computer- readable medium in which a computer program is stored which, when being executed by a processor, is adapted to control or carry out a method having the above mentioned features.
  • Figure 1 shows schematically a perspective view of an X-ray imaging system according to a first embodiment of the present invention in which one X-ray detector is sandwiched between two X-ray sources;
  • Figure 2 shows in an unrolled representation the X-ray sources and the X-ray detector of the imaging system of Figure 1;
  • Figure 3 shows a sectional view of the imaging system of Figure 1;
  • Figure 4 shows a sectional view of a modified imaging system in which the X-ray source is located at a larger radial distance than the X-ray detector;
  • Figure 5 shows a sectional view of a modified imaging system in which the X-ray source is located at a smaller radial distance than the X-ray detector;
  • Figure 6 illustrates the elimination of a shadow zone in the imaging system of Figures 3 to 5 by shifting the X-ray detector and source axially;
  • Figure 7 shows in an unrolled representation the X-ray sources and the X-ray detector of an alternative imaging system, in which these components extend about less than 360°;
  • Figure 8 illustrates the fan angle ⁇
  • Figure 9 shows in an unrolled representation the X-ray source and the X-ray detectors of an imaging system according to another embodiment of the present invention in which one X-ray source is sandwiched between two X-ray detectors;
  • Figure 10 illustrates the elimination of a shadow zone in the imaging system of Figure 9 by shifting the X-ray detector and source axially;
  • Figure 11 shows in an unrolled representation the X-ray source and the X-ray detectors of an alternative imaging system, in which these components extend about less than 360°.
  • CNT carbon nanotubes
  • the present invention proposes designs of X-ray imaging systems that are particularly (but not exclusively) suited in combination with the use of X-ray sources comprising carbon nanotubes.
  • at least one stationary anode equipped with multiple CNT emitters as corresponding cathode, such that a large number of focal spots (FS) can be achieved along the anode tracks.
  • FS focal spots
  • the discrete FS positions will be neglected in the following, treating them instead as a continuous FS-trajectory (FST).
  • FSTs and two- dimensional detectors on cones, particularly on cylinders (which are considered here as special types of cones, i.e. cones with a cone angle of 0°) with a common axis, wherein the scanned object is placed within these cones/cylinders.
  • Figure 1 shows schematically in a perspective view a first embodiment of a medical X-ray imaging system 100 that realizes the aforementioned principles.
  • the imaging system 100 comprises:
  • the term “cone” shall comprise the special cases of a circle (i.e. all focal spots lying on a circle or section of a circle) and a cylinder (i.e. all focal spots lying on a cylinder or a part of its surface).
  • the shape of a cone in the narrower sense (with cone angle ⁇ 0°) may particularly be used for constructive reasons in X-ray sources with some axial extension in z-direction, e.g. to make the anode areas accessible to electron beams (cf. designs described in US 2002/0094064 Al).
  • An X-ray detector 130 shaped as a cylinder with its sensitive area lying on a (cylindrical) "detector cone” about the system axis A.
  • the X-ray detector 130 is axially positioned adjacent to the first X-ray source 110.
  • the geometrical objects "source cone” SC and “detector cone” DC are cylinders of the same diameter in this embodiment.
  • a second X-ray source 120 that is of substantially the same design as the first X-ray source 110 with its focal spots also located on the source cone. Moreover, the second X-ray source 120 is axially located adjacent to the X-ray detector 130 such that the latter is sandwiched between the two X-ray sources 110 and 130.
  • a controller 150 that is coupled to the two X-ray sources 110 and 120 for controlling the activation of focal spots 111 according to a given program.
  • the controller is also coupled to the X-ray detector 130 for generally controlling the generation of X-ray images and for processing the acquired image data.
  • the controller 150 may at least partially be realized by digital data processing hardware with associated software stored in a suitable memory (e.g. RAM, EPROM, hard disc, CD, DVD, etc.).
  • Figure 2 shows the X-ray sources 110, 120 and the intermediate X-ray detector 130 unrolled in a plane, i.e.
  • the upper and lower edges are actually connected to form a three-dimensional cylinder (more strictly speaking, the unrolled representation shows only the X-ray emitting and X-ray sensitive areas of the X-ray source and the X-ray detector, respectively). Both the X-ray sources and the X-ray detector extend in this configuration over 360°.
  • Figure 3 shows a section (comprising the system axis A) through the X-ray sources 110, 120 and the X-ray detector 130 of the imaging system 100.
  • X-rays generated at focal spots 111 of the X-ray sources 110, 120 are also shown in the Figure. They impinge on the sensitive areas 131 in the opposing region of the X-ray detector 130.
  • both the focal spots 111 and the sensitive areas 131 are necessarily mounted in a housing 112 and 132, respectively, there is always some axial distance between them.
  • a central "shadow zone" SZ remains on the system axis A that is not transmitted by detectable X-ray beams.
  • Figure 4 shows in a sectional view like Figure 3 a modified imaging system 200 in which the aforementioned central shadow zone SZ is reduced in size by arranging the X-ray sources 210 and 220 on a cylindrical source cone SC with a larger diameter (i.e. a larger radial x-distance from the system axis A) than the diameter of the cylindrical detector cone DC of the X-ray detector 230.
  • Figure 5 shows in a sectional view like Figure 3 another modified imaging system 300 that realizes a similar solution.
  • the cylindrical detector cone DC of the X-ray detector 330 has a larger diameter than the cylindrical source cone SC of the X-ray sources 310 and 320 (and an increased axial extension, too). Again, a considerable reduction of the central shadow zone SZ can be achieved.
  • Figure 6 illustrates this (for the imaging system 100 of Figures 1 to 3) for two exposures made from positions of the X-ray sources and X-ray detector that are axially (i.e. in z-direction) shifted by a pitch ⁇ z of a helical scan.
  • the shadow zone is completely eliminated if the pitch ⁇ z is identical to the distance between detector and anode.
  • the illumination pattern of a step-and-shoot method is the same with the same pitch.
  • the required movement is slow compared to the rotation of a conventional CT system.
  • the axial movement can either be realized with a movement of the acquisition system or a proper movement of the scanned object.
  • anodes of the X-ray sources 410, 420 cover an angular range of 180°+ ⁇ and the detector 430 covers an angular range of 180°+ ⁇ , a short scan acquisition and reconstruction can be performed, wherein the angular intervals of the anode and the detector must be opposed as shown in Figure 7.
  • Figure 7 further illustrates by dashed lines additional detector areas 430' that can optionally be arranged at the axial position of the X-ray sources 410, 420 in areas which are not occupied by these sources (i.e. between 270°+ ⁇ /2 and 90°- ⁇ /2).
  • the additional areas 430' extend the X-ray detector in z-direction and allow to collect more measurement data with the same applied X-ray dose.
  • Figure 7 illustrates by dashed lines additional X-ray emitting areas 410' that can optionally be arranged at the axial position of the X-ray detector 430 in areas which are not occupied by this detector (i.e. between 90°+ ⁇ /2 and 270°- ⁇ /2).
  • the additional areas 410' extend the X-ray source in z-direction and may be used to improve the image quality.
  • Figure 8 shows the fan angle ⁇ for a beam emitted from a focal spot 411.
  • a central field of view FOV
  • X-ray are detected within an angle range 430 covered by the detector.
  • the imaging systems of the previously described embodiments comprise one X-ray detector sandwiched between two X-ray sources.
  • Figure 9 shows in the unrolled representation an alternative design of an imaging system 500 in which one X-ray source 510 is sandwiched between two X-ray detectors 530 and 540.
  • Figure 10 a illustrates for this imaging system 500 the illumination pattern generated by X-rays emitted from focal spots 511 for a single axial position. It can be seen that there is also a central shadow zone that is not covered by X-rays.
  • Figure 11 shows in the unrolled representation an imaging system 600 that differs from the previous one in that the X-ray source 610 and the X-ray detectors 630 and 640 both only extend over 180°+ ⁇ . Thus a short scan acquisition and reconstruction can again be performed.
  • the Figure shows additional detection areas 630' that are optionally arranged in axial overlap with the X-ray source 610 at circumferential angles outside the range of the source 610 (i.e. between 270°+ ⁇ /2 and 90°- ⁇ /2).
  • additional X-ray emitting areas 610' are shown that are optionally arranged in axial overlap with the X-ray detectors 630, 640 in areas which are not occupied by these detectors (i.e. between 90°+ ⁇ /2 and 270°- ⁇ /2).
  • the invention addresses a fundamental problem of static CT scanners which comes from the fact that the detector and the focal spot FS cannot be at the same axial position.
  • the problem grows with the minimal axial distance of the FS and the detector given by mechanical constrains (e.g. minimal axial distance of outermost detector element to the detector housing). If the source cone and the detector cone have different diameters, the potential shadowing can be reduced by reducing the effective gap to the mechanical border of one of the components.
  • the inherent advantage of the proposed systems with the capability to randomly switch the position of the focal spots is that the order of the measured projections must not follow the continuous movement of a scanner mechanics anymore. This allows better sampling strategies e.g. for cardiac or functional imaging.
  • the systems are particularly suited for pre-clinical CT (animal CT) and interventional imaging (C-Arm like systems).

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Abstract

L'invention porte sur un système d'imagerie par rayons X (100) de type tomodensitomètre. Dans un mode de réalisation préféré du système, un détecteur cylindrique de rayons X (130) est pris en sandwich entre deux sources cylindriques de rayons X (110, 120) ou inversement. De préférence, les sources de rayons X comprennent des cathodes munies de nanotubes de carbone et d'une multitude de points focaux (111) qui peuvent être sélectivement commandés. Les diamètres du cylindre de la source de rayons X et du détecteur de rayons X peuvent être identiques ou, de préférence, différents. De plus, la source de rayons X et le détecteur de rayons X s'étendent, de préférence, de manière périphérique sur moins de 360°.
PCT/IB2008/053353 2007-08-31 2008-08-21 Système d'imagerie par rayons x avec un agencement cylindrique de source et de détecteur WO2009027904A2 (fr)

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WO2022179387A1 (fr) * 2021-02-26 2022-09-01 清华大学 Système d'imagerie pour examen radiographique

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Publication number Priority date Publication date Assignee Title
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WO2022179387A1 (fr) * 2021-02-26 2022-09-01 清华大学 Système d'imagerie pour examen radiographique

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