Classifications

• • 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
  • H01J35/08—Anodes; Anti cathodes
  • H01J35/10—Rotary anodes; Arrangements for rotating anodes; Cooling rotary anodes
• • 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
  • G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
  • G21K1/04—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using variable diaphragms, shutters, choppers
  • G21K1/043—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using variable diaphragms, shutters, choppers changing time structure of beams by mechanical means, e.g. choppers, spinning filter wheels

Definitions

• the present invention relates to X-ray imaging, and more particularly, an X-ray imaging system having a non-stationary anode for improved field of view imaging.
• Vacuum tubes including rotating anodes bombarded by energetic electrons are well developed and extensively used, particularly as X-ray tubes where the anode includes a rotating X-ray emitting track bombarded by electrons from a cathode.
• the anode is rotated so at any instant only a small portion thereof is bombarded by the electrons.
• the energetic electrons are distributed over a relatively large surface area.
• the anode may also need to be cooled using a running liquid that removes heat from the anode.
• the rotating anode of a typical X-ray system provides merely a stationary beam; that is to say the X-ray beam is always pointed at one particular location on the target.
• the use of a rotating anode within the X-ray tube has not, heretofore, been used to expand the imaging field of view, while maintaining low power requirements.
• An improved system and associated method are provided for increasing the field of view of an X-ray imaging system, while maintaining low power requirements.
• the disclosure provides for increasing the field of view in an X-ray imaging system by using an X-ray tube having a dynamic anode, which provides a non-stationary X-ray beam.
• the dynamic anodes of the present disclosure which provides a non-stationary X-ray beam, allows for a more uniform and wider inspection area or field of view (compared to systems using anodes, which provide stationary X-ray beams).
• an X-ray imaging system includes an X-ray tube including, a cathode for emitting electrons; and a dynamic anode.
• the dynamic anode receives the electrons from the cathode and generates an X-ray beam that is non-stationary.
• the dynamic anode rotates between a first position where the X-ray beam is directed at a first location on an object and a second position where the X-ray beam is directed at a second location on the object to generate the non-stationary beam.
• a method for imaging. The method includes providing an X-ray tube having a moveable anode; and moving the moveable anode between a first position where the moveable anode directs an X-ray beam at a first location on an object to a second position where the moveable anode directs an X-ray beam at a second location on the object.
• dynamic anodes may operate at approximately 1/10 the wattage of a conventional X-ray imaging system; this also improves the life of the dynamic anode.
• using a dynamic anode may reduce the size of the X-ray tube which may result in a less hazardous X-ray tube that is more environmentally friendly as less radiation is emitted and less of the X-ray beam is lost when compared to a typical X-ray tube with a stationary anode.
• Smaller X-ray tubes require less shielding so that the resulting X-ray imaging system may be lighter, smaller and more portable.
• the use of a smaller X-ray tube to radiate objects limits the focus of the emissions, thus less power is lost in the form of heat and X-rays not being used to create an image.
• Another advantage of using dynamic anodes is it allows for a larger, more parallel X- ray fan without loss in X-ray photon density or an increase in geometric unsharpness.
• Geometric unsharpness occurs when an X-ray fan emanating from an anode is too wide. This also results in a reduction of contrast at the edge of the fan.
• the present disclosure provides for the use of a small focal spot size, which equates to a sharper image and higher resolution.
• the system is compact and lightweight so that it can be easily transported and used within confined spaces or in environments where weight is a consideration, such as inside or underneath aircraft. Because systems and structures in aircraft environments have various orientations and limitations to access, the system is portable and adaptable.
• FIG. 1 is a simplified schematic top view of a typical X-ray tube having an anode which delivers a stationary X-ray beam;
• FIGS. 2 A, 2B and 2C are simplified schematic top views of an X-ray tube having an anode which delivers a non-stationary X-ray beam, according to one embodiment of the disclosure;
• FIG. 3 is a simplified schematic side view of the X-ray tube of FIG. 2A;
• FIG. 4 is a simplified schematic top view of a typical X-ray backscatter system having an anode which delivers a stationary X-ray beam;
• FIG. 5 is a simplified schematic top view of an X-ray backscatter system having an anode which delivers a non-stationary X-ray beam, according to one embodiment of the disclosure
• FIG. 6 is a simplified schematic view of the internal structure of an X-ray tube having an oscillating anode, according to one embodiment of the disclosure.
• FIG. 7 is a simplified schematic view of the internal structure of an X-ray tube having a rotating anode, according to one embodiment of the disclosure.
• FIG. 1 is a simplified top view of a typical X-ray imaging system 100, including an
• X-ray tube 102 and an anode 104 which provides only a stationary X-ray beam (hereinafter "stationary anode 104").
• X-ray tube 102 is a vacuum tube and includes a cathode 302 (FIG. 3) which emits electrons into the vacuum.
• Stationary anode 104 collects the electrons, establishing a flow of electrical current through X-ray tube 102.
• To generate the X- ray beam electrons are boiled off the cathode by means of thermo-ionic-emission, and are collided with the anode under a high energy electric field. X-rays are produced when the electrons are suddenly decelerated upon collision with the anode.
• the bombarding electrons have sufficient energy, they can knock an electron out of an inner shell of the target metal atoms. Then, electrons from higher states drop down to fill the vacancy, emitting X-ray photons with precise energies determined by the electron energy levels and generating an X- ray fan with the maximum flux of the beam at the center of the cone.
• the beam is radially symmetric within a circular fan or cone of X-rays.
• Stationary anode 104 generates the X-ray beam 106, which is emitted out from X-ray tube 102 through window 108.
• X-ray beam 106 provides instantaneous coverage 'L' to the extent of cone angle ⁇ .
• the volume of electron bombardment and X-ray generation required to provide full coverage L of object 110 requires a large amount of power and creates large amounts of heat, which in turn requires a large cooling system. By requiring large amounts of power and a large cooling system, the size of X-ray tube 102 must also be large.
• top and bottom portions Xj and X2 of object 110 lie outside cone angle ⁇ and are therefore not subject to examination by X-ray beam 106.
• a detector (not shown) would not receive data related to portions Xi and X 2 and these portions are therefore not included in any X-ray images generated of object 110.
• FIGS. 2A, 2B, 2C are simplified schematic top views and FIG. 3 is a simplified side view, of an X-ray imaging system 200 in accordance with an embodiment of the disclosure.
• X-ray imaging system 200 includes X-ray tube 202 having dynamic anode 204, a cathode 302, and a continuous window 206, which allows for up to a 360 ° emission of X-ray beam 208 for a wider area of imaging.
• cathode 302 emits electrons into the vacuum of X-ray tube 202.
• Dynamic anode 204 collects the electrons to establish a flow of electrical current through X- ray tube 202.
• Dynamic anode 204 generates an X-ray beam 208 that emits through window 206 in X-ray tube 202 to create an image of object 110 under examination.
• dynamic anode 204 is an anode that is made to move within X- ray tube 202, such that X-ray beam 208 is made to scan across object 110.
• dynamic anode 204 may be pointed in a first direction, such as toward top portion Xj. While pointed at position Xi, beam 208 covers a portion dYi of object 110, which is proportional to the width of beam 208. As shown in FIG. 2B, dynamic anode 204 may then be rotated as indicated by arrow
• dynamic anode 204 may continue to rotate until beam 208 is pointed in a second direction, such as toward bottom portion X 2 of object 110, covering the incremental portion dY. In this manner, beam 208 is made to image the entire length (Xi + X2 + L) at increments dY.
• the rate of rotation of dynamic anode 204 may be set to any desired rate which provides adequate imaging for an intended purpose. In one embodiment, the rate of rotation of dynamic anode 204 may range from about 5 revs/sec to about 25 revs/sec.
• Dynamic anode 204 may be made to rotate or otherwise move to provide a non- stationary beam using any conventional means, such as a motor and gear arrangement and the like inside of the X-ray tube.
• an X-ray backscatter system which includes an X-ray tube (vacuum tube) that generates photons, and at least one silicon-based detector or photo-multiplier tube.
• X-ray tube vacuum tube
• silicon-based detector or photo-multiplier tube At least one silicon-based detector or photo-multiplier tube.
• photons emerge from the source or anode in a collimated "flying spot" beam that scans vertically.
• Backscattered photons are collected in the detector(s) and used to generate two-dimensional or three-dimensional images of objects. The angle over which the spot travels is limited by the X-ray fan angle coming off the anode.
• FIG. 4 is a simplified top view of a typical X-ray backscatter system 400, including an X-ray tube 402 and an anode 404, which provides only a stationary X-ray beam (hereinafter "stationary anode 404").
• Stationary anode 404 generates the X-ray beam 406, which is emitted from X-ray tube 402 through window 408.
• a rotating collimator 410 having an aperture 412, encircles X- ray tube 402 and rotates around stationary anode 404 such that aperture 412 rotates across the length of window 408.
• a portion of X-ray beam 406 passes through aperture 412 as aperture 412 rotates across window 408.
• stationary anode 404 X-ray directs beam 406 to the internal side of collimator 410.
• Beam 406 impinges on collimator 410 to the extent of cone angle ⁇ .
• aperture 412 of collimator 410 passes through beam 406 a small portion 416 of beam 406 passes through to provide coverage on object 414. Since most of beam 406 is not used to impinge on to object 414, the power used to generate beam 406 is wasted.
• FIG. 5 is a simplified illustration of an operational embodiment of an X-ray system 500, including dynamic anode 502, which can be made to rotate within the X-ray tube, for example, in the direction of arrow 512.
• X-ray system 500 also includes continuous window 506, and a rotating collimator 508 having aperture 510, which surrounds dynamic anode 502.
• beam 504 is directed through aperture 510 to impinge on object 414 as rotating collimator 508 rotates about anode 502.
• the X-rays back-scattered from the object are picked up by a photo multiplier tube or solid state detector (not shown), which generates electric signals that can be used to produce an image.
• the relative rotation of dynamic anode 502 and of rotating collimator 508 is linked. Accordingly, in this embodiment, aperture 510 can be made to rotate in constant alignment with dynamic anode 502.
• X-ray beam 504 may be directed specifically at aperture 510 during the entire imaging operation. Because beam 504 is concentrated directly in the vicinity of aperture 510 during the entire imaging operation, the concentration 512 of beam 504 which actually passes through aperture 510 represents a large percentage of the actual beam 504.
• the efficiency associated with using a more concentrated beam 504 continuously directed at aperture 510 as collimator 508 and anode 502 rotate allows for using a smaller anode with a less powerful beam.
• the smaller anode allows the dimensions of the X-ray tube to also be reduced, because of the lower size and power requirements.
• beam 504 continuously at aperture 510 during an imaging operation also allows for complete circumferential beam coverage to cover a larger area of inspection with a larger field of view.
• X-ray beam 504 may be made to obtain a more concentrated X-ray at a particular location.
• FIG. 6 is a simplified schematic view of the internal structure of an X-ray system including an X-ray tube having an oscillating anode, according to one embodiment of the disclosure.
• anode 602 may be made to oscillate, for example, as opposed to rotate.
• Oscillating anode 602 collects electrons represented by arrows 604 while oscillating back and forth about a central axis 606 of the X-ray tube.
• oscillating anode 602 increases the X-ray photon lobe angle without reducing the total number of photons per square centimeter.
• X-ray beam 608 is then emitted from oscillating anode 602 generating an X-ray fan area 610, such that X-ray beam 608 is made to sweep across an object continuously to the endpoints of the oscillation.
• oscillating anode 602 allows for an instantaneous increase or decrease in the field-of-view (as represented by X-ray fan area 610), depending on the angle of oscillation ⁇ , which may be as large as 120°.
• FIG. 7 is a simplified schematic view of the internal structure of an X-ray tube having a rotating polygon shaped anode, according to one embodiment of the disclosure.
• Rotating polygon shaped anode 702 includes faceted sides for changing the angle of incidence of an X-ray beam and the corresponding X-ray beam lobe 704 and curved scanned range 706 that result.
• the location of electron bombardment and X- ray generation is distributed so that the angle of incidence of the X-ray beam and the corresponding X-ray beam lobe 704 and curved scanned range 706 that result are changed.
• the principles and teachings described herein may be applied to a variety of structures and/or systems, such as aircraft, spacecraft, ground and ocean-going vehicles, complex facilities such as power generation for both commercial and government applications, power plants, processing plants, refineries, military applications, and transportation systems, including, but not limited to, automobiles, ships, helicopters, and trains.
• the present disclosure may be used for homeland security, as a personnel inspection system (portal) to look for hidden weapons under clothing or in luggage, borescopic applications, such as inspection work where the area to be inspected is inaccessible by other means and in the medical field or where a 360° field of view is required.
• the X-ray tube can penetrate very large objects, such as vehicles, by going inside the engine compartment or fuel tank which a normal X-ray imaging system cannot access due to size.

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• Physics & Mathematics (AREA)
• Spectroscopy & Molecular Physics (AREA)
• Engineering & Computer Science (AREA)
• General Engineering & Computer Science (AREA)
• High Energy & Nuclear Physics (AREA)
• X-Ray Techniques (AREA)
• Analysing Materials By The Use Of Radiation (AREA)

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• 2007
  • 2007-05-03 US US11/744,115 patent/US7529343B2/en active Active
  • 2007-05-04 JP JP2009509743A patent/JP5175841B2/ja active Active
  • 2007-05-04 CA CA2650479A patent/CA2650479C/en active Active
  • 2007-05-04 AU AU2007248520A patent/AU2007248520B2/en active Active
  • 2007-05-04 WO PCT/US2007/010843 patent/WO2007130576A2/en not_active Ceased
  • 2007-05-04 ES ES07756210.6T patent/ES2374316T5/es active Active
  • 2007-05-04 AT AT07756210T patent/ATE534921T1/de active
  • 2007-05-04 EP EP07756210.6A patent/EP2013643B2/en active Active

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