US3752990A - X-ray device having an anode tube with filtering means thereon - Google Patents

X-ray device having an anode tube with filtering means thereon Download PDF

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Publication number
US3752990A
US3752990A US00154530A US3752990DA US3752990A US 3752990 A US3752990 A US 3752990A US 00154530 A US00154530 A US 00154530A US 3752990D A US3752990D A US 3752990DA US 3752990 A US3752990 A US 3752990A
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tube
anode
anode tube
ray
filtering
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H Fischer
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    • 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
    • A61B6/51—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 dentistry
    • A61B6/512—Intraoral means
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/24—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof
    • H01J35/26—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof by rotation of the anode or anticathode
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/32—Tubes wherein the X-rays are produced at or near the end of the tube or a part thereof which tube or part has a small cross-section to facilitate introduction into a small hole or cavity
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05G—X-RAY TECHNIQUE
    • H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
    • H05G1/02—Constructional details
    • H05G1/04—Mounting the X-ray tube within a closed housing
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05G—X-RAY TECHNIQUE
    • H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
    • H05G1/02—Constructional details
    • H05G1/04—Mounting the X-ray tube within a closed housing
    • H05G1/06—X-ray tube and at least part of the power supply apparatus being mounted within the same housing

Definitions

  • the anode tube which projects from the housing is preferably shielded when not in use by a projecting tube slidabie relative to the housing.
  • the device may also include a second X-ray tube for intra-oral and extra-oral photography with this second tube emitting X- rays at to the axis of the hollow anode X-ray tube.
  • Prefiltering material may be provided on the head of the anode tube or the head of the anode tube may be specially shaped so that uniform prefiltering of the radiation from the anode tube occurs over the beam angle necessary for full-mouth photography.
  • This invention relates to devices for use in producing X-ray photographs, particularly dental X-ray photographs.
  • the invention is particularly concerned with devices for use in producing dental X-ray photographs which make use of special hollow-anode X-ray tubes which are quite distinct in construction and function from the usual diagnostic X-ray tubes.
  • the whole electrode system comprising a cathode emitting the electrons, a control electrode affect ing the focussing, and a usually conical anode arranged in the anode tube with a collecting or focussing coil mounted on the anode tube and also affecting the focussing of the electron stream is so constructed that it is formed from two or three mechanically completely separate electrode units as far as adjustment of the system is concerned.
  • the focal spot is created at the end of a hollow-anode tube externally of the actual X-ray tube casing and with a conical anode it is at the cone tip pointing towards the cathode.
  • the focal spot of the tube must be kept very small on account of the comparatively small focal length necessitate by these photographic techniques and on account of the lack of sharpness in the image which would otherwise arise, with the result that the electrode system of such a tube must be extremely accurately focussed and adjusted initially and must then remain so.
  • the danger of the tube becoming out of adjustment is greater the smaller the diameter of the anode tube and the more sensitive the electrode system of the X-ray tube.
  • the user of such tubes protects the very highly sensitive anode tube, which is formed from very soft annealed copper at those places where in the event of a mechanical stress the greatest bending moment is exerted, by placing a protective cap over the tube housing in the inactive position of the device to protect the anode tube from damage and defocussing.
  • the protective cap is removed in all cases.
  • the casing of the hollow-anode X-ray tube is rigidly connected to mounting means to which is connected resilient support means, said support means being secured to the housing and extending between the housing and the casing of the hollow-anode X-ray tube.
  • the X-ray tube casing including the part of the anode tube adjacent to the cathode is preferably formed of a ceramic based material, such as a ceramic oxide for example, since this provides the anode tube with substantially higher resistance to bending stresses than the copper components previously generally used.
  • any prefiltering of the radiation within the radiation beam angle should be constant. This is not the case in the presently known hollowanode constructions in which the anode tubes and/or the applicators placed over the tubes have a constant wall thickness in the vicinity of the source of the emitted radiation, with the result that the X-rays follow different length paths in their passage through the wall in dependence on the angle at which they are emitted and are consequently subjected to differential filtering.
  • This disadvantage is overcome in accordance with a preferred feature of the present invention by the provision of prefiltering material on the head of the anode tube containing the anode, the distribution being such that uniform perfiltering of the radiation occurs over the whole beam angle necessary for full-mouth examination.
  • This may be achieved by making the wall at the head of the anode tube of non-uniform thickness such that all X-rays passing through the tube wall at whatever angle traverse equal length paths through the tube wall.
  • this additional prefiltering material being provided in such a way that the X-rays which on the basis of their angle of emission traverse a shorter path length through the tube wall pass through a greater mass of prefiltering material than the X-rays which traverse a longer path length.
  • a device equipped with a hollow-anode X-ray tube which is also such that distortion free photographs of individual objects can be achieved with it as with the known intraoral and extra-oral photographic techniques.
  • this is achieved by providing a second X-ray tube for intra-oral and extra-oral photographs within the housing of the device and in addition to the hollow-anode X-ray tube, the direction of emission of radiation from the second tube being at an angle of substantially 90 to the longitudinal axis of the hollow-anode X-ray tube.
  • a high voltage transformer for both tubes is preferably also mounted within the housing of the device so that in this case the device can be described as a one-piece instrument.
  • a double X-ray tube suitable both for full-mouth photography and also for intraand extra-oral photography, such as double X-ray tube having two separate cathode filaments in a common casing. This results in a system which can be made extremely compact.
  • a device using two separate X-ray tubes has the possible advantage that the X-ray tubes may be of a simpler and cheaper construction and that in the event of failure of one complete X-ray system or one X-ray tube the other X-ray system is still usable until replacement or repair of the failed system or tube.
  • the casing When using a common tube casing for both X-ray systems the casing may be secured to mounting means which includes an electron reflection target in alignment with the cathode filament for the said second X-ray tube and a side window through which X-rays from the target are beamed.
  • FIG. I is a cross-sectional view through a part of a first embodiment of device in accordance with the invention, the device comprising a hollow-anode X-ray tube, here shown in its inactive position;
  • FIG. 2 is a similar cross-sectional view of the device shown in FIG. I but with the hollow-anode X-ray tube in its operational position;
  • FIG. 3 is a similar cross-sectional view through a second embodiment of device in accordance with the invention, this device comprising a double X-ray tube adapted both for panoramic full-mouth photography and also for intra-oral and extra-oral photography, and with the device here shown in its operational position for the last-mentioned photographic technique;
  • FIG. 4 is a longitudinal sectional view through the head of the anode tube of a hollow-anode X-ray tube
  • the upper half (A) of the illustrated tube being of known form and the lower half (B) of the illustrated tube being of modified novel form;
  • FIG. 5 is a longitudinal sectional view through the head of the hollow-anode X-ray tube illustrating the radiation beam-angle necessary for panoramic full-mouth examination and of interest in relation to prefiltering considerations;
  • FIG. 6 is a schematic longitudinal sectional view through a third embodiment of device in accordance with the invention, the device here comprising two separate X-ray tube systems;
  • FIG. 7 is a front end elevational view of the device of FIG. 6;
  • FIG. 8 is a schematic longitudinal sectional view through a fourth embodiment of device in accordance with the invention, again comprising two separate Xray tube systems; and,
  • FIG. 9 is a front end elevational view of the device of FIG. 8.
  • the X-ray tube comprises a casing 16 fitted with an anode tube 9 carrying a conical anode 17; a mount 1 at anode potential and rigidly connected to the tube casing 16; and a focussing unit 5 which is fixedly connected to the tube system.
  • the mount 1 is connected to a housing 4 of the device by means of a resilient link 2, for example in the form of a spring element.
  • a high voltage generator (not shown) for the X-ray tube is mounted in a suitable manner within the housing 4 of the device.
  • a protecting tube 15 is provided which is secured so as to be displaceable in the axial direction over the housing 4 of the device.
  • this protecting tube 15 is shown in its operative protective position enclosing the anode tube 9.
  • the tube 15 is provided with an aperture I8 in its end face to provide for passage of the anode tube 9 therethrough.
  • Additional springs 7 are provided between the housing 4 and the mount 1 on the tube casing 16 in order to adjust the flexibility and resiliency of the link 2 so thatit will absorb forces arising as a result of impacts or pressures on the anode tube 9 and will return the tube system to its original setting as soon as such foreign external forces no longer act on the anode tube.
  • the protecting tube 15 has been withdrawn back over the housing 4 of the device so that the anode tube 9 is located in its operational position in which it can be inserted into the mouth if panoramic photography of the whole of a patients mouth is to be carried out.
  • the embodiment of the invention which is shown in FIG. 3 comprises a double X-ray tube by means of which it is possible to use both the hollow-anode technique for panoramic full-mouth photography and also intra oral and extra-oral photographic techniques for examination of individual teeth.
  • a tube side window 11 with an electron target disc 10 arranged adjacent thereto are provided in the mount 1 as a part of the tube casing 16, in addition to the anode tube 9 which has the anode 17 as anelectron target point.
  • a filament arrangement 13 acting as the cathode associated with the anode l7 and a filament arrangement 14 acting as the cathode associated with the electron target disc 10 are provided within the tube casing 16.
  • the mount 1 is at anode potential.
  • the cathode filaments 13 and 14 which are necessary for the two electrode systems are mounted on a cathode support 12 and can be selectively switched on individually according to the desired type of photographic examination to be effected with the device.
  • apertures are provided in the housing 4 and in the axially displaceable protecting tube 15 for the passage of the X-rays emitted through the tube side window 11. These apertures are so arranged that when the device is used for hollow-anode photographic examination the protecting tube 15 masks the aperture in the housing 4 in front of the side window 11 and uncovers the free end of the anode tube 9, while when the device is used for intra-oral or extraoral photographic examination the protecting tube 15 encloses the free end of the anode tube 9 and unmasks the side window 11.
  • FIG. 4 of the drawings shows the head of a known form of hollow-anode X-ray tube in which the anode tube 9 is cylindrical and of uniform wall thickness in the radiating region.
  • the X-rays coming from the anode 17 within a beam angle a and which do not pass through the wall of the anode tube at i'ight-angles along the line S for example rays passing along the lines S1 to S4, must penetrate larger amounts ofthe material of the anode tube.
  • These rays are therefore prefiltered differentially and this has an extremely unfavourable effect on the quality of the image on the X-ray photograph.
  • FIG. 5 shows, in relation to an anode tube 9 with a conical anode l7 and fitted with an applicator 8 over the anode tube, the tube and applicator being shown inserted into a patients mouth, that the beam angle 0: shown in FIG. 4 is in fact necessary for full-mouth photographic examination.
  • the cylindrical wall of the anode tube may have its thickness unchanged.
  • this additional prefiltering material may be provided on the applicator 8 which is slidable over the anode tube 9, or it may be provided partially on this applicator and partially on the anode tube itself.
  • the X-ray tube casing including the part of the anode tube adjacent to the cathode, is preferably made from a ceramic-based material having high resistance to bending stresses.
  • a ceramic-based material having high resistance to bending stresses.
  • the best materials are ceramic oxides, particularly beryllium oxide, which can absorb large bending moments and which at the same time are permeable to the magnetic field necessary for focussing the electron stream.
  • this resilient supporting link need not necessarily consist of a spring element, but for example can alternatively be in the form of resilient membranes, or in the form of ball and socket joints in association with individual springs spaced on a circle around the tube.
  • the arrangement is such that the reaction to bending stresses of the resilient link due to forces acting from externally on the anode tube 9 is smaller than the reaction to deformation of the anode tube 9 due to the external forces acting thereon.
  • Focussing unit 5 shown in FIGS. 1 to 3 may be an electromagnetic unit or a permanent magnet system. It will further be appreciated that an electrostatic focus sing unit could alternatively be used.
  • a hollow-anode X-ray tube suitable for full mouth or panoral photographic examination and comprising the X-ray tube casing 16, the anode tube 9, and an associated transformer 6 mounted on an axis 19 which is parallel to but displaced upwardly relative to the longitudinal axis 20 of the housing 4 of the device.
  • Parallel to this tube 9, 16 is provided an intra-oral tube 21 having its longitudinal axis 22 displaced downwardly relative to the longitudinal axis 20 of the housing 4 of the device.
  • the direction 23 of the emitted radiation from the intra-oral X-ray tube 21 is at to the longitudinal axis 19 of the hollow-anode X-ray tube 9, 16.
  • the hollow-anode X-ray tube 9, 16 is resiliently mounted in the housing 4 by means of springs or a spring bellows or a membrane 2.
  • a protecting tube 15 is provided to protect the anode tube 9.
  • the protecting tube 15 is displaceable along the axis of the X-ray tube such that its cylindrical wall is displaceably positioned within the housing 4 and only its forward end wall portion provided with an aperture 25 for the anode tube 9 lies outside the housing 4.
  • a window 24 for the passage of radiation from the intra-oral tube 21 is provided in the cylindrical wall portion of the protecting tube 15. This window 24 is only aligned with the output from the intra-oral tube 21 when the hollowanode X-ray tube 9, 16 is not operational and is enclosed by the protecting tube 15. However, the window 24 is not in alignment with the axis 23 of the radiation from the tube 21 when the protecting tube 15 is displaced inwardly and the hollow-anode X-ray tube 9 extends in its operative position.
  • FIGS. 8 and 9 only differs from that shown in FIGS. 6 and 7 in that the two X-ray tubes 9, 16 and 21 are not arranged one below the other but are positioned on a common axis 22 one behind the other within the housing 3.
  • the housing 3 is not cylindrical but has an inverted teardrop shape cross-section.
  • the hollow-anode the housing which is of larger cross-section.
  • the direction 23 of the emitted radiation from the intra-oral tube 21 makes an angle of 90 with the longitudinal axis 19 of the hollow-anode X-ray tube 9, 16.
  • the casing of the intra-oral or extra-oral X-ray tube 21 preferably consists of a ceramic oxide with the tube side window being formed from sintered beryllium oxide.
  • anode tube means projecting from said tube housing, said tube means having a longitudinal axis;
  • an anode mounted in said anode tube means adjacent the end of said anode tube means opposite said tube housing, said anode, when bombarded by electrons, emitting X-rays over a beam angle that extends both radially and longitudinally of said anode tube means to produce a full-mouth radiograph when said anode tube means is correctly positioned within a patients mouth;
  • said anode tube means comprises filtering means, said filtering means having a variable thickness along the longitudinal axis of said tube means such that the X-rays pass through substantially equal thicknesses of filtering material irrespective of the emission angle relative to the longitudinal axis of said anode tube means whereby the X-rays are uniformly filtered over the entire beam angle.
  • said filtering means comprises a first portion of filtering material of uniform thickness forming said anode tube means and a second portion of filtering material of varying thickness covering preselected areas of said first portion of filtering material wherein said second portion of filtering material provides additional filtering to said X-ray radiation such that said X-ray radiation travels equal path lengths within said filtering means.
  • said anode tube means comprises:
  • an anode tube of cylindrical cross sectioning having walls of uniform thickness wherein said walls comprise said first portion of said filtering means;
  • an applicator tube for covering at least a portion of said anode tube means, surrounding said at least a portion of said anode tube, wherein said second portion of said filtering means is affixed to said applicator tube.
  • said anode tube means comprises:
  • said filtering means comprises a first portion disposed of said anode tube and a second portion disposed on said applicator.
  • said anode tube means is formed from a ceramic based material such as a ceramic oxide.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Engineering & Computer Science (AREA)
  • Optics & Photonics (AREA)
  • Biomedical Technology (AREA)
  • Biophysics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Dentistry (AREA)
  • Pathology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • X-Ray Techniques (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
US00154530A 1970-06-22 1971-06-18 X-ray device having an anode tube with filtering means thereon Expired - Lifetime US3752990A (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE2030624A DE2030624B2 (de) 1970-06-22 1970-06-22 Röntgenstrahier mit einer Hohlanoden-Röntgenröhre für zahnmedizinische Röntgenaufnahmen
DE19712123617 DE2123617A1 (de) 1970-06-22 1971-05-12 Einrichtung zur Herstellung von Röntgenaufnahmen, insbesondere zahnärztlichen Röntgenaufnahmen

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DE (2) DE2030624B2 (enExample)
FR (1) FR2109627A5 (enExample)
GB (1) GB1312039A (enExample)
NL (1) NL7108491A (enExample)

Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4006361A (en) * 1974-12-18 1977-02-01 Atomic Energy Of Canada Limited X-ray beam flattener
US4057733A (en) * 1975-02-17 1977-11-08 Siemens Aktiengesellschaft Dental X-ray diagnostic installation
US4286167A (en) * 1979-05-14 1981-08-25 Varian Associates, Inc. Multi-element X-ray equalizing filter
US5369679A (en) * 1990-09-05 1994-11-29 Photoelectron Corporation Low power x-ray source with implantable probe for treatment of brain tumors
US5422926A (en) * 1990-09-05 1995-06-06 Photoelectron Corporation X-ray source with shaped radiation pattern
US5452720A (en) * 1990-09-05 1995-09-26 Photoelectron Corporation Method for treating brain tumors
US5566221A (en) * 1994-07-12 1996-10-15 Photoelectron Corporation Apparatus for applying a predetermined x-radiation flux to an interior surface of a body cavity
US5621780A (en) * 1990-09-05 1997-04-15 Photoelectron Corporation X-ray apparatus for applying a predetermined flux to an interior surface of a body cavity
US5854822A (en) * 1997-07-25 1998-12-29 Xrt Corp. Miniature x-ray device having cold cathode
US6069938A (en) * 1998-03-06 2000-05-30 Chornenky; Victor Ivan Method and x-ray device using pulse high voltage source
US6095966A (en) * 1997-02-21 2000-08-01 Xrt Corp. X-ray device having a dilation structure for delivering localized radiation to an interior of a body
US6108402A (en) * 1998-01-16 2000-08-22 Medtronic Ave, Inc. Diamond vacuum housing for miniature x-ray device
US6195411B1 (en) 1999-05-13 2001-02-27 Photoelectron Corporation Miniature x-ray source with flexible probe
US6215852B1 (en) 1998-12-10 2001-04-10 General Electric Company Thermal energy storage and transfer assembly
US6285735B1 (en) 2000-02-11 2001-09-04 Photoelectron Corporation Apparatus for local radiation therapy
US6301328B1 (en) 2000-02-11 2001-10-09 Photoelectron Corporation Apparatus for local radiation therapy
US6353658B1 (en) 1999-09-08 2002-03-05 The Regents Of The University Of California Miniature x-ray source
US6377846B1 (en) 1997-02-21 2002-04-23 Medtronic Ave, Inc. Device for delivering localized x-ray radiation and method of manufacture
US6421416B1 (en) 2000-02-11 2002-07-16 Photoelectron Corporation Apparatus for local radiation therapy
US6799075B1 (en) 1995-08-24 2004-09-28 Medtronic Ave, Inc. X-ray catheter
US7109505B1 (en) 2000-02-11 2006-09-19 Carl Zeiss Ag Shaped biocompatible radiation shield and method for making same
US20090304158A1 (en) * 2008-06-06 2009-12-10 Kristopher John Frutschy Modular multispot x-ray source and method of making same
US20100098218A1 (en) * 2008-10-16 2010-04-22 Vermilyea Mark E Apparatus for providing shielding in a multispot x-ray source and method of making same
US20100098219A1 (en) * 2008-10-16 2010-04-22 Vermilyea Mark E Apparatus for providing collimation in a multispot x-ray source and method of making same
US20120025106A1 (en) * 2009-04-14 2012-02-02 Manfred Apel Beam head
EP2768289A1 (de) * 2013-02-18 2014-08-20 Astrium GmbH Röntgenvorrichtung mit personentransportablem Strahlungsmodul
US9173623B2 (en) 2013-04-19 2015-11-03 Samuel Soonho Lee X-ray tube and receiver inside mouth
US20220317064A1 (en) * 2021-03-30 2022-10-06 Digiray Corp. Tube weld x-ray inspection device
US11874236B2 (en) 2021-03-30 2024-01-16 Digiray Corp. Tube weld x-ray inspection device

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FR2534066B1 (fr) * 1982-10-05 1989-09-08 Thomson Csf Tube a rayons x produisant un faisceau a haut rendement, notamment en forme de pinceau
DE10313863B4 (de) * 2003-03-21 2006-01-19 Siemens Ag Röntgenstrahlaustrittsfenster, insbesondere für Megalixröhren
DE102010009276A1 (de) * 2010-02-25 2011-08-25 Dürr Dental AG, 74321 Röntgenröhre sowie System zur Herstellung von Röntgenbildern für die zahnmedizinische oder kieferorthopädische Diagnostik

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US1881448A (en) * 1928-08-15 1932-10-11 Formell Corp Ltd X-ray method and means
US2748293A (en) * 1951-09-08 1956-05-29 Hartford Nat Bank & Trust Co Irradiation applicator for X-ray therapy
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US1881448A (en) * 1928-08-15 1932-10-11 Formell Corp Ltd X-ray method and means
US2748293A (en) * 1951-09-08 1956-05-29 Hartford Nat Bank & Trust Co Irradiation applicator for X-ray therapy
US2946892A (en) * 1958-01-22 1960-07-26 Foerderung Forschung Gmbh Arrangement for controlling and correcting the location of the focal spot produced by a cathode-ray on the target of a roentgen-tube

Cited By (41)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4006361A (en) * 1974-12-18 1977-02-01 Atomic Energy Of Canada Limited X-ray beam flattener
US4057733A (en) * 1975-02-17 1977-11-08 Siemens Aktiengesellschaft Dental X-ray diagnostic installation
US4286167A (en) * 1979-05-14 1981-08-25 Varian Associates, Inc. Multi-element X-ray equalizing filter
US5528652A (en) * 1990-09-05 1996-06-18 Photoelectron Corporation Method for treating brain tumors
US5621780A (en) * 1990-09-05 1997-04-15 Photoelectron Corporation X-ray apparatus for applying a predetermined flux to an interior surface of a body cavity
US5422926A (en) * 1990-09-05 1995-06-06 Photoelectron Corporation X-ray source with shaped radiation pattern
US5442678A (en) * 1990-09-05 1995-08-15 Photoelectron Corporation X-ray source with improved beam steering
US5452720A (en) * 1990-09-05 1995-09-26 Photoelectron Corporation Method for treating brain tumors
US5369679A (en) * 1990-09-05 1994-11-29 Photoelectron Corporation Low power x-ray source with implantable probe for treatment of brain tumors
US5428658A (en) * 1994-01-21 1995-06-27 Photoelectron Corporation X-ray source with flexible probe
US5566221A (en) * 1994-07-12 1996-10-15 Photoelectron Corporation Apparatus for applying a predetermined x-radiation flux to an interior surface of a body cavity
JP2927966B2 (ja) 1994-07-12 1999-07-28 フォトエレクトロン コーポレイション 体腔の内層表面に予め定められたフラックスを加えるためのｘ線装置
US6799075B1 (en) 1995-08-24 2004-09-28 Medtronic Ave, Inc. X-ray catheter
US6095966A (en) * 1997-02-21 2000-08-01 Xrt Corp. X-ray device having a dilation structure for delivering localized radiation to an interior of a body
US6377846B1 (en) 1997-02-21 2002-04-23 Medtronic Ave, Inc. Device for delivering localized x-ray radiation and method of manufacture
US5854822A (en) * 1997-07-25 1998-12-29 Xrt Corp. Miniature x-ray device having cold cathode
US6108402A (en) * 1998-01-16 2000-08-22 Medtronic Ave, Inc. Diamond vacuum housing for miniature x-ray device
US6069938A (en) * 1998-03-06 2000-05-30 Chornenky; Victor Ivan Method and x-ray device using pulse high voltage source
US6301332B1 (en) 1998-12-10 2001-10-09 General Electric Company Thermal filter for an x-ray tube window
US6215852B1 (en) 1998-12-10 2001-04-10 General Electric Company Thermal energy storage and transfer assembly
US6320932B2 (en) 1999-05-13 2001-11-20 Photoelectron Corporation Miniature radiation source with flexible probe and laser driven thermionic emitter
US6195411B1 (en) 1999-05-13 2001-02-27 Photoelectron Corporation Miniature x-ray source with flexible probe
US6353658B1 (en) 1999-09-08 2002-03-05 The Regents Of The University Of California Miniature x-ray source
US6301328B1 (en) 2000-02-11 2001-10-09 Photoelectron Corporation Apparatus for local radiation therapy
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US20090304158A1 (en) * 2008-06-06 2009-12-10 Kristopher John Frutschy Modular multispot x-ray source and method of making same
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US20100098218A1 (en) * 2008-10-16 2010-04-22 Vermilyea Mark E Apparatus for providing shielding in a multispot x-ray source and method of making same
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US7976218B2 (en) 2008-10-16 2011-07-12 General Electric Company Apparatus for providing shielding in a multispot x-ray source and method of making same
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US8946657B2 (en) * 2009-04-14 2015-02-03 Siemens Aktiengesellschaft Beam head
EP2768289A1 (de) * 2013-02-18 2014-08-20 Astrium GmbH Röntgenvorrichtung mit personentransportablem Strahlungsmodul
WO2014124938A1 (de) * 2013-02-18 2014-08-21 Astrium Gmbh Röntgenvorrichtung mit personentransportables strahlungsmodul
US9173623B2 (en) 2013-04-19 2015-11-03 Samuel Soonho Lee X-ray tube and receiver inside mouth
US20220317064A1 (en) * 2021-03-30 2022-10-06 Digiray Corp. Tube weld x-ray inspection device
US11860113B2 (en) * 2021-03-30 2024-01-02 Digiray Corp. Tube weld X-ray inspection device comprising an X-ray source, an X-ray source support, and an image plate fixing part for fixing an image plate
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Also Published As

Publication number Publication date
FR2109627A5 (enExample) 1972-05-26
GB1312039A (en) 1973-04-04
DE2123617A1 (de) 1972-11-16
DE2030624A1 (de) 1972-03-16
DE2030624B2 (de) 1980-10-09
NL7108491A (enExample) 1971-12-24

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