WO2010146504A1 - X-ray tube for generating two focal spots and medical device comprising same - Google Patents
X-ray tube for generating two focal spots and medical device comprising same Download PDFInfo
- Publication number
- WO2010146504A1 WO2010146504A1 PCT/IB2010/052578 IB2010052578W WO2010146504A1 WO 2010146504 A1 WO2010146504 A1 WO 2010146504A1 IB 2010052578 W IB2010052578 W IB 2010052578W WO 2010146504 A1 WO2010146504 A1 WO 2010146504A1
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- WIPO (PCT)
- Prior art keywords
- electron
- ray tube
- anode
- switchable
- ray
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Classifications
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
- H01J35/04—Electrodes ; Mutual position thereof; Constructional adaptations therefor
- H01J35/045—Electrodes for controlling the current of the cathode ray, e.g. control grids
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
- H01J35/04—Electrodes ; Mutual position thereof; Constructional adaptations therefor
- H01J35/06—Cathodes
- H01J35/066—Details of electron optical components, e.g. cathode cups
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/56—Switching-on; Switching-off
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J2235/00—X-ray tubes
- H01J2235/06—Cathode assembly
- H01J2235/068—Multi-cathode assembly
Definitions
- the present invention relates to an X-ray tube for generating two focal spots on an anode. Furthermore, the invention relates to a medical device comprising such X-ray tube. BACKGROUND OF THE INVENTION
- a high power X-ray tube typically includes an evacuated envelope or housing which holds a cathode filament through which a heating current or filament current is passed in order to serve as an electron emitter for thermionic emission of electrons.
- a high electrical potential typically in the order of 100 to 200 kV, is applied between the cathode and the anode which are also located within the evacuated envelope. This potential causes a tube current or beam of electrons to flow from the cathode to the anode through the evacuated region in the interior of the evacuated envelope.
- the electron beam impinges on a small area of a focal spot of the anode with sufficient energy to generate X-rays.
- the X-rays may then be transmitted through an object to be observed such as a patient. While a portion of the X- rays will be absorbed within the object, the transmitted X-rays may be detected by an X-ray detector arranged at an opposite side of the object.
- High quality CT scanners may use a movement of the focal spot to double the resolution of the imaging system.
- a cathode is provided for emitting an electron beam towards a rotating disk-shaped anode such that a focal spot is generated on a slanted X-ray emitting surface of the anode.
- the generated X-rays are emitted in a direction substantially perpendicular to a direction of the impinging electron beam.
- a focal spot which can be moved in a direction of the anode's rotating axis in order to be able to generate two distinct focal spots.
- This direction typically coincides with a direction of the impinging electron beam and is usually referred to as y-direction.
- a direction perpendicular to the y- direction i.e. the typical direction of the emitted X-rays from the anode towards the X-ray window of the X-ray tube and then towards the patient is usually referred to as z-direction.
- a direction perpendicular to both, the y-direction and the z-direction, i.e. a direction tangential to the rotating anode disk, is usually referred to as x-direction.
- the desired movement of the focal spot and of the emitted X-ray beam in y-direction may be obtained by a movement of the electron beam in the z-direction, i.e. in a direction towards the detector.
- One method of focal spot control employs electrostatic grids or biasing electrodes associated to a single electron emitting filament of the cathode. Voltages on the two electrostatic grids may be varied to change the location as well as the width of an electron beam impinging on the focal track of the rotating anode.
- electrostatic grids for controlling both, the position and the width of a focal spot may require a special complex and expensive grid design.
- Another method of focal spot control may employ a magnetic yoke in order to create a magnetic field that affects a path of an electron beam emitted from the anode.
- a magnetic yoke in order to create a magnetic field that affects a path of an electron beam emitted from the anode.
- the provision of magnetic yokes within a housing of an X-ray tube may require a special expensive design of the whole X-ray tube.
- the magnetic yoke tube requires two additional connections to be passed through the X-ray tube housing, making it incompatible with many CT systems.
- the magnetic fields employed to deflect and focus the electron beam may not be moved in a square wave fashion between the two focal spot positions, thereby potentially creating a gap in the collected X-ray detection data.
- an improved X-ray tube design allowing to overcome at least some of the above-described deficiencies of prior art approaches.
- an X-ray tube having a simple structural design while allowing to generate two distinct focal spots.
- such improved X-ray tube design which is compatible with many conventional X-ray systems and may therefore be integrated into such X-ray systems with only small changes.
- an X-ray tube comprising a cathode and an anode.
- the cathode comprises a first electron emitter adapted for emitting a first electron beam for generating a first focal spot on the anode and a second electron emitter adapted for emitting a second electron beam for generating a second focal spot on the anode.
- each electron emitter comprises its own associated switchable grid for blocking the respective emitted electron beam.
- This first aspect of the present invention may be seen as based on the following idea:
- the present invention proposes to provide two separate electron emitters for enabling a generation of two separate electron beams which impinge on the anode at distinct focal spots.
- each of the electron emitters of the cathode comprises its associated switchable grid.
- This switchable grid which is sometimes also referred to as grid switch, is adapted for blocking electrons emitted from the respective electron emitter from reaching the anode.
- each switchable grid may be adapted such that upon electrostatically charging the grid, an electrical field is established such that an electrical acceleration field otherwise existing between the cathode and the anode is locally blocked, i.e. is prevented from reaching the respective electron emitter. Accordingly, when the switchable grid is switched to a blocking state or ON state, no electrons are accelerated from the associated electron emitter towards the respective focal spot on the anode.
- a simple X-ray tube design may be provided in which different focal spots may be generated on an anode's X-ray emitting surface by electron beams each coming from one of a plurality of electron emitters, wherein each focal spot may be activated or disactivated by non-blocking (OFF state) or blocking (ON state) the electron beam emitted by the respective electron emitter using the associated switchable grid.
- the switchable grids may be activated or disactivated very fast, it may be possible to very rapidly switch between an X-ray beam coming from the first focal spot and an X-ray beam coming from the second focal spot.
- By rapidly switching between the two distinct X-ray beams during acquisition for example in a rotating CT scanner two different images in the patient plane may be acquired by alternately projecting X-ray beams through the patient at slightly displaced projection directions. Thereby, the overall resolution of an X-ray image acquired by a multi- pixel X-ray detector may be significantly enhanced.
- the cathode of the X-ray tube comprises at least one first electron emitter and at least one second electron emitter.
- Each of the electron emitters may be provided as heatable filaments which may be heated to substantial temperatures of e.g. more than 1000 0 C such as to thermionically emit electrons.
- other types of electron emitters may be used such as electron emitters based on electric field emission.
- the electron emitters may be adapted, for example due to their geometric structure, due to their geometric arrangement and/or due to the electric field applied between the cathode and the anode, for emitting respective electron beams in a y-direction towards an X-ray emitting surface of the anode. Thereby, a focal spot may be generated at the X-ray emitting surface.
- the anode may be provided with a shape of a disk and may be adapted for rotating around the y-direction. On such rotating anode, a focal spot will travel along a focal track on a circumference of the disk-shaped anode. Accordingly, the thermal energy absorbed within the focal spot due to the impinging electrons will be distributed along the focal track thereby reducing any cooling requirements for the anode's focal spot region.
- the anode may have an X-ray emitting surface which is arranged such as to emit X-rays substantially in a z-direction perpendicular to the y-direction upon incidence of an electron beam on a focal spot.
- the X-ray emitting surface may be slanted, i.e. arranged at an angle of e.g. between 78° and 84° , with respect to the y-direction.
- the first and second electron emitters are displaced with respect to each other in the z-direction.
- geometric centres of the first electron emitter and of the second electron emitter are spaced apart from each other when projected in the z- direction. Due to such displaced or spaced apart arrangement of the first and second electron emitters in the z-direction, the electron beams emitted in the y-direction from the first and second electron emitters will impinge onto the slanted X-ray emitting surface of the anode with a certain displacement in z-direction as well.
- each X-ray beam may create an X-ray projection through an object to a detector arranged at an opposite side of the object. Having two X-ray beam paths may allow doubling the information detected by the X-ray detector thereby significantly increasing the resolution of acquired X-ray images.
- the first and second electron emitters are adapted such that the first and second focal spots are aligned in an x-direction.
- the x-direction is perpendicular to both, the y-direction and the z-direction.
- the first and second focal spots may be displaced in a z-direction, they shall preferably be aligned, i.e. not displaced, in the x-direction.
- Such alignment in x-direction may be obtained by specifically arranging the first and second electron emitters together with their associated switchable grids.
- each electron emitter may be provided as a longitudinal heatable filament extending in the z-direction.
- the filaments of the first and second electron emitters may be arranged parallel to each other at a specific distance to each other in x-direction and with a specific displacement in z-direction.
- the filament and its associated switchable grid of the first electron emitter may be arranged at an angle with respect to the filament and its associated switchable grid of the second electron emitter. Accordingly, the first electron beam is emitted at an angle with respect to the second electron beam. The angle may be chosen such that the first and second electron beams impinge onto the X-ray emitting surface of the anode along a line in the x- direction such that the first and second focal spots are aligned in the x-direction.
- the first and second electron emitters are adapted such that the first and second focal spots overlap in the z-direction.
- the areas of the first and second focal spots may nevertheless overlap in z-direction as may be the case if the extension of the focal spots in z-direction is larger than the displacement between the focal spots in z-direction.
- the switchable grids associated to each of the first and second electron emitters are adapted to be operated independent of each other.
- the switchable grid associated to the first electron emitter may be switched OFF thereby allowing transmission of electrons from the first electron emitter to the anode
- the switchable grid associated to the second electron emitter may be independently operated for example to an ON-state in which electrons emitted from the second electron emitter are blocked from travelling to the anode. Accordingly, by switching the switchable grids to an ON-state or OFF-state, the respective focal spots may be independently switched ON or OFF.
- the switchable grids associated to one of the first and second electron emitters may be adapted to be electrostatically charged such as to locally shield an electrical field between the anode and the cathode from reaching the respective electron emitter.
- an electrical voltage may be applied to the switchable grids such as to establish an electrical potential which at least compensates the electrical field between the anode and the cathode such that in the neighbourhood of the electron emitter there is no electrical field accelerating electrons in a direction towards the anode.
- Such function of selectively blocking or passing electrons by specifically influencing an electric field may be realized by specifically adapting a geometry and arrangement of grid plates of each switchable grid as well as by specifically selecting voltages applied to the grid plates.
- the switchable grid associated to one of the first and second electron emitters may comprise two electrostatically chargeable grid plates arranged on opposite sides of the respective electron emitter.
- a voltage supplied by control to the switchable grid may be used to thereby control an x-deflection and/or a width of an associated focal spot.
- the applied voltage may be controlled such as to influence an electrical field in the neighbourhood to the switchable grid in order to thereby control the path and/or focusing of the respective electron beam emitted by the electron emitter.
- the grids associated to the first and second electron emitters respectively may be arranged at an angle to one another such as to emit first and second electron beams with respective x-deflections such that the generated first and second focal spots are aligned along the x-direction.
- the X-ray tube comprises a control which is adapted for applying a blocking voltage to at least one of the switchable grids of the first and second electron emitters.
- a control which is adapted for applying a blocking voltage to at least one of the switchable grids of the first and second electron emitters.
- at least one of the switchable grids associated to the first and second electron emitters is switched to an ON-state such as to block any electron beam from a respective electron emitter. Accordingly, at most one of the first and second focal spots is irradiated at a given point in time and the first and second focal spots are not irradiated simultaneously.
- the control is adapted for either applying a blocking voltage to the switchable grid of the first electron emitter or for applying a blocking voltage to the switchable grid of the second electron emitter.
- the control periodically alternately applies a blocking voltage to the switchable grid of the first electron emitter and to the switchable grid of the second electron emitter.
- Such blocking voltages may be alternately applied at switching frequencies of for example more than 4 kHz, preferably more than 1OkHz.
- the first focal spot and the second focal spot may be alternately operated such that X- ray beams are alternately emitted along a first X-ray beam path and a second X-ray beam path slightly displaced with respect to the first X-ray beam path.
- X-ray beams are alternately emitted along a first X-ray beam path and a second X-ray beam path slightly displaced with respect to the first X-ray beam path.
- the switching frequency with which different X-ray beams are operated alternately may be chosen as high as to thereby generate additional imaging information due to the two distinct projections through the object in order to thereby increase the overall resolution of the CT scanning system.
- a medical device comprising an X-ray tube as described above is proposed.
- the medical device may be any medical X-ray device such as for example a high quality CT X-ray scanner.
- Fig. 1 shows a CT scanner.
- Fig. 2 shows a schematical representation of X-ray projections within a CT scanner using an X-ray tube according to an embodiment of the present invention.
- Fig. 3 shows a perspective view of a cathode assembly of an X-ray tube according to an embodiment of the present invention.
- Fig. 4 shows a plan view onto the cathode assembly of Fig. 3.
- Fig. 5 shows a perspective view of a cathode-anode assembly in an X-ray tube according to an embodiment of the present invention.
- Fig. 6 shows a plan view onto the anode of the assembly shown in Fig. 5. All figures are only schematical representations and not to scale. Same reference signs in the figures refer to same or similar features.
- Fig. 1 shows basic components of an exemplary medical device 100 in a form of a computer tomography scanner as used in medical facilities.
- the CT scanner comprises an examination table 130 suitable for positioning an object, for example a patient, of which projection images are to be taken.
- the CT scanner further comprises a rotatable gantry 105 suitable for rotation around the examination table 130.
- the examination table 130 is arranged substantially in the centre of the gantry 105.
- the CT scanner further comprises an X-ray source 120 and a detector 110.
- the X-ray tube and the detector 110 are diametrically arranged on the gantry 105.
- the gantry 105 rotates around the examination table 130 while the X-ray source 120 emits X-rays.
- the emitted X-rays interact with the object deposited on the examination table 130 and the interacting X-rays are then incident on the detector 110.
- the incident X-rays define a pattern of points of intensities which are digitally transformed into a corresponding pattern of pixels.
- the pattern of pixels is then available as the projection image of the examined object.
- the digital projection image can then be stored and/or post-processed by suitable software to be viewable on a monitor. For example, the slices obtained from the detection results acquired at one revolution of the gantry may be used to calculate a 3D image of the object.
- Fig. 2 shows a schematic representation of the arrangement of an X-ray tube 1 serving as an X-ray source 120, a patient lying on an examination table 130 and an X-ray detector 110 arranged at an opposite side.
- the X-ray tube 1 comprises a housing 3.
- the housing 3 encloses a vacuum space 5 in which a cathode 7 and an anode 9 are arranged.
- the anode has a disk-shape and can be rotated around the rotation axis 11 and may be driven by a motor 13.
- the cathode 7 comprises a first electron emitter 15 for emitting a first electron beam 17 and a second electron emitter 19 for emitting a second electron beam 21.
- the first and second electron beams 17, 21 impinge onto a slanted X-ray emitting surface 23 of the anode 9 and thereby generate respective first and second focal spots 25, 21.
- the first and second electron emitters 15, 19 are displaced with respect to each other in the z-direction and emit electron beams 17, 21 in the y-direction.
- the first and second beams 17, 21 spaced apart in the z-direction impinge onto respective first and second spots 25, 27 which are displaced with respect to each other in the y-direction.
- the distance between the first and second electron beams 17, 21, the z- direction, i.e. in a radial direction of the disk-shaped anode 9 may be for example 4.5 mm
- the distance of the resulting focal spots 25, 27 in the y-direction, i.e. in an axial direction of the anode 9, may be approximately 0.7 mm.
- a first X-ray beam 29 is emitted in the z-direction.
- This X-ray beam 29 is transmitted through the patient and the resulting X-ray projection is detected in pixels or slices 112 of a one-dimensional X-ray detector 110.
- a second X-ray beam 31 is emitted in the z-direction, transmitted through the patient and detected with the detector 110.
- the first and second focal spots 25, 27 are displaced in the y-direction by a distance of approximately 0.7 mm, an image displacement within the patient of approximately 0.35 mm may occur.
- an additional slice projection through the patient may be acquired.
- the distance or thickness of acquired slice projections may be approximately 0.7 mm, the resolution of such CT scanner may be doubled by providing an additional slice projection at a displacement in y-direction of approximately 0.35 mm.
- Figs. 3 and 4 show a perspective view and a top view of a cathode 7 to be used in an X-ray tube 1 according to an embodiment of the present invention.
- the cathode 7 comprises two heatable filaments 33, 35 serving as first and second electron emitters 15, 19.
- Each filament 33, 35 has an associated switchable grid 37, 39.
- Each switchable grid comprises grid switch plates 41, 43 and 45, 47, respectively arranged at opposite sides of the filament 33, 35.
- the grid switch plates 41, 43, 45, 47 are made from an electrically conductive material such as a metal and may be charged to such electrical potential such as to block or shield an electrical field between the cathode 7 and the anode 9 from reaching the electron emitters 15, 19.
- the focal spots 25, 27 are aligned with respect to an x-direction. While, as can be seen in Figs.
- the first and second electron emitters 15, 19 are spaced apart from each other in the x-direction, such alignment of the focal spots 25, 27 in x- direction may be achieved by arranging the first electron emitter 15 and its associated switchable grid 37 on a surface 49 of the cathode 7 which is tilted at an angle ⁇ of approximately 20 to 50° with respect to a surface 51 of the cathode 7 on which the second electron emitter 19 and its associated switchable grid 39 are arranged.
- the first and second electron beams 17, 21 are emitted in directions having an angle ⁇ with respect to each other such that the electron beams 17, 21 impinge onto focal spots 25, 27 which are aligned in x-direction.
- the focal spots 25, 27 have a rectangular, longitudinal shape and overlap along the z-direction.
- a control 53 for energizing and controlling the electron emitters 15, 19 and the switchable grids 37, 39 is adapted to apply a blocking voltage at least to one of the switchable grids 37, 39 at any point in time such that only one of the focal spots 25, 27 is irradiated by electrons at a given point in time.
- the control 53 may periodically switch one of the switchable grids 37, 39 from an OFF-state to an ON-state and back while alternately switching the other switchable grid 39, 37 from an ON-state to an OFF-state and back at a frequency of for example 10 kHz.
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- X-Ray Techniques (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
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Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2012515593A JP5675794B2 (en) | 2009-06-17 | 2010-06-10 | X-ray tube for generating two focal spots and medical device having the same |
EP10728350.9A EP2443643B1 (en) | 2009-06-17 | 2010-06-10 | X-ray tube for generating two focal spots and medical device comprising same |
CN201080027182.1A CN102804325B (en) | 2009-06-17 | 2010-06-10 | For generation of X-ray tube and the medical treatment device comprising this X-ray tube of two focal spots |
US13/319,612 US9142381B2 (en) | 2009-06-17 | 2010-06-10 | X-ray tube for generating two focal spots and medical device comprising same |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP09162949 | 2009-06-17 | ||
EP09162949.3 | 2009-06-17 |
Publications (1)
Publication Number | Publication Date |
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WO2010146504A1 true WO2010146504A1 (en) | 2010-12-23 |
Family
ID=42697207
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/IB2010/052578 WO2010146504A1 (en) | 2009-06-17 | 2010-06-10 | X-ray tube for generating two focal spots and medical device comprising same |
Country Status (5)
Country | Link |
---|---|
US (1) | US9142381B2 (en) |
EP (1) | EP2443643B1 (en) |
JP (1) | JP5675794B2 (en) |
CN (1) | CN102804325B (en) |
WO (1) | WO2010146504A1 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
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WO2013144771A2 (en) | 2012-03-26 | 2013-10-03 | Koninklijke Philips N.V. | Simulated spatial live viewing of an object from variable view-points |
WO2014006556A1 (en) | 2012-07-05 | 2014-01-09 | Koninklijke Philips N.V. | Temporal alignment of and signal-to-noise-ratio enhancment in image streams for multi-channel x-ray imaging |
US20160217965A1 (en) * | 2015-01-28 | 2016-07-28 | Varian Medical Systems, Inc. | X-ray tube having a dual grid and dual filament cathode |
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US8831178B2 (en) * | 2012-07-03 | 2014-09-09 | General Electric Company | Apparatus and method of manufacturing a thermally stable cathode in an X-ray tube |
US10373792B2 (en) | 2016-06-28 | 2019-08-06 | General Electric Company | Cathode assembly for use in X-ray generation |
DE102016222365B3 (en) * | 2016-11-15 | 2018-04-05 | Siemens Healthcare Gmbh | A method, computer program product, computer readable medium and apparatus for generating x-ray pulses in x-ray imaging |
KR102158776B1 (en) * | 2017-01-03 | 2020-09-23 | 한국전자통신연구원 | Electron emission source and x-ray generator using the same |
JP6885803B2 (en) * | 2017-06-27 | 2021-06-16 | ゼネラル・エレクトリック・カンパニイ | Radiation imaging device and imaging method |
EP3531437A1 (en) * | 2018-02-27 | 2019-08-28 | Siemens Healthcare GmbH | Electron-emitting device |
KR102131665B1 (en) * | 2018-12-21 | 2020-07-08 | 주식회사 씨에이티빔텍 | Dual x-ray source unit and dual x-ray apparatus |
US20230197397A1 (en) * | 2021-12-21 | 2023-06-22 | GE Precision Healthcare LLC | X-ray tube cathode focusing element |
CN116959940B (en) * | 2023-09-20 | 2023-12-29 | 上海超群检测科技股份有限公司 | Cathode assembly of X-ray tube and X-ray tube |
Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3946261A (en) * | 1975-01-03 | 1976-03-23 | The Machlett Laboratories, Inc. | Dual filament X-Ray tube |
GB2034967A (en) * | 1978-11-02 | 1980-06-11 | Tokyo Shibaura Electric Co | Stereoscopic x-ray device |
EP0588432A1 (en) * | 1992-09-16 | 1994-03-23 | Philips Patentverwaltung GmbH | X-ray apparatus including an X-ray generator and an X-ray tube having at least two electron sources |
US20060002515A1 (en) * | 2004-05-28 | 2006-01-05 | General Electric Company | System for forming x-rays and method for using same |
WO2007116329A1 (en) * | 2006-04-07 | 2007-10-18 | Philips Intellectual Property & Standards Gmbh | Dual spectrum x-ray tube with switched focal spots and filter |
WO2007142999A2 (en) * | 2006-05-31 | 2007-12-13 | L-3 Communications Security And Detection Systems, Inc. | Dual energy x-ray source |
DE102009044302A1 (en) * | 2008-10-24 | 2010-04-29 | General Electric Company | System and method for fast peak high voltage switching for two-energy CT |
Family Cites Families (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS5776800A (en) * | 1980-10-30 | 1982-05-13 | Toshiba Corp | X-ray cinematographic stereographic unit |
JP2579912B2 (en) * | 1986-08-05 | 1997-02-12 | キヤノン株式会社 | Charged particle generator |
JPH05314935A (en) * | 1992-05-13 | 1993-11-26 | Hitachi Medical Corp | Rotary anode x-ray tube and x-ray device using it |
JPH0963520A (en) * | 1995-08-22 | 1997-03-07 | Shimadzu Corp | X-ray tube |
US5621781A (en) * | 1995-12-14 | 1997-04-15 | General Electric Company | X-ray tube |
US5844963A (en) * | 1997-08-28 | 1998-12-01 | Varian Associates, Inc. | Electron beam superimposition method and apparatus |
US6480572B2 (en) * | 2001-03-09 | 2002-11-12 | Koninklijke Philips Electronics N.V. | Dual filament, electrostatically controlled focal spot for x-ray tubes |
US7221740B2 (en) | 2004-06-30 | 2007-05-22 | Glenayre Electronics, Inc. | Auto block and auto discovery in a distributed communication system |
JP5295503B2 (en) * | 2007-01-15 | 2013-09-18 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | X-ray generator and X-ray CT apparatus |
JP5460318B2 (en) * | 2007-07-19 | 2014-04-02 | 株式会社日立メディコ | X-ray generator and X-ray CT apparatus using the same |
US8311186B2 (en) * | 2007-12-14 | 2012-11-13 | Schlumberger Technology Corporation | Bi-directional dispenser cathode |
JP5150338B2 (en) * | 2008-03-31 | 2013-02-20 | 小林製薬株式会社 | Blister container |
-
2010
- 2010-06-10 WO PCT/IB2010/052578 patent/WO2010146504A1/en active Application Filing
- 2010-06-10 US US13/319,612 patent/US9142381B2/en not_active Expired - Fee Related
- 2010-06-10 EP EP10728350.9A patent/EP2443643B1/en not_active Not-in-force
- 2010-06-10 CN CN201080027182.1A patent/CN102804325B/en active Active
- 2010-06-10 JP JP2012515593A patent/JP5675794B2/en active Active
Patent Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3946261A (en) * | 1975-01-03 | 1976-03-23 | The Machlett Laboratories, Inc. | Dual filament X-Ray tube |
GB2034967A (en) * | 1978-11-02 | 1980-06-11 | Tokyo Shibaura Electric Co | Stereoscopic x-ray device |
EP0588432A1 (en) * | 1992-09-16 | 1994-03-23 | Philips Patentverwaltung GmbH | X-ray apparatus including an X-ray generator and an X-ray tube having at least two electron sources |
US20060002515A1 (en) * | 2004-05-28 | 2006-01-05 | General Electric Company | System for forming x-rays and method for using same |
WO2007116329A1 (en) * | 2006-04-07 | 2007-10-18 | Philips Intellectual Property & Standards Gmbh | Dual spectrum x-ray tube with switched focal spots and filter |
WO2007142999A2 (en) * | 2006-05-31 | 2007-12-13 | L-3 Communications Security And Detection Systems, Inc. | Dual energy x-ray source |
DE102009044302A1 (en) * | 2008-10-24 | 2010-04-29 | General Electric Company | System and method for fast peak high voltage switching for two-energy CT |
Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2013144771A2 (en) | 2012-03-26 | 2013-10-03 | Koninklijke Philips N.V. | Simulated spatial live viewing of an object from variable view-points |
US9967961B2 (en) | 2012-03-26 | 2018-05-08 | Koninklijke Philips N.V. | Simulated spatial live viewing of an object from variable view-points |
WO2014006556A1 (en) | 2012-07-05 | 2014-01-09 | Koninklijke Philips N.V. | Temporal alignment of and signal-to-noise-ratio enhancment in image streams for multi-channel x-ray imaging |
CN104427939A (en) * | 2012-07-05 | 2015-03-18 | 皇家飞利浦有限公司 | Temporal alignment of and signal-to-noise-ratio enhancement in image streams for multi-channel X-ray imaging |
US10887492B2 (en) | 2012-07-05 | 2021-01-05 | Koninklijke Philips N.V. | Temporal alignment of and signal-to-noise-ratio enhancment in image streams for multi-channel x-ray imaging |
US20160217965A1 (en) * | 2015-01-28 | 2016-07-28 | Varian Medical Systems, Inc. | X-ray tube having a dual grid and dual filament cathode |
WO2016123405A1 (en) * | 2015-01-28 | 2016-08-04 | Varian Medical Systems, Inc. | X-ray tube having a dual grid for steering and focusing the electron beam and dual filament cathode |
US9779907B2 (en) | 2015-01-28 | 2017-10-03 | Varex Imaging Corporation | X-ray tube having a dual grid and dual filament cathode |
Also Published As
Publication number | Publication date |
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EP2443643B1 (en) | 2016-12-14 |
US9142381B2 (en) | 2015-09-22 |
JP2012530340A (en) | 2012-11-29 |
US20120082300A1 (en) | 2012-04-05 |
EP2443643A1 (en) | 2012-04-25 |
CN102804325A (en) | 2012-11-28 |
JP5675794B2 (en) | 2015-02-25 |
CN102804325B (en) | 2016-03-23 |
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