EP2850634B1 - Appareil de radiothérapie - Google Patents

Appareil de radiothérapie Download PDF

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Publication number
EP2850634B1
EP2850634B1 EP13723919.0A EP13723919A EP2850634B1 EP 2850634 B1 EP2850634 B1 EP 2850634B1 EP 13723919 A EP13723919 A EP 13723919A EP 2850634 B1 EP2850634 B1 EP 2850634B1
Authority
EP
European Patent Office
Prior art keywords
radiotherapy apparatus
rod
anode
electron beam
shaped conduit
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP13723919.0A
Other languages
German (de)
English (en)
Other versions
EP2850634A1 (fr
Inventor
Keith Albert Spanswick
George Andrew LEEDER
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Ariane Medical Systems Ltd
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Ariane Medical Systems Ltd
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Publication date
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Publication of EP2850634A1 publication Critical patent/EP2850634A1/fr
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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
    • H01J35/08—Anodes; Anti cathodes
    • H01J35/12—Cooling non-rotary anodes
    • H01J35/13—Active cooling, e.g. fluid flow, heat pipes
    • 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
    • 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
    • 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
    • H01J35/112—Non-rotating anodes
    • H01J35/116—Transmissive anodes
    • 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
    • H01J35/12—Cooling non-rotary anodes

Definitions

  • This invention relates to the field of radiotherapy apparatus, particularly for the treatment of human cancers.
  • radiotherapy apparatus in the form of a rod anode X-ray tube of the known type illustrated in Figure 1 .
  • the rod anode X-ray tube consists of a vacuum chamber 10 containing an emissive filament 11 and a rod structure 12 terminated with a high density metal target or transmission anode 13.
  • the filament 11 is connected to a high voltage generator 15 which is grounded by grounded anode 16.
  • the filament typically consists of a coiled tungsten wire that is heated until white hot when electrons are liberated from the surface. Electrons emitted from the filament 11 are focussed along a desired path by a focus electrode 14.
  • the rod structure 12 is a rod-shaped electron beam conduit or drift tube through which the electron beam travels from the filament to the anode.
  • X-rays are produced when the electrons, attracted by the strong positive charge (typically 50 kV) of the anode 13, collide with the anode's surface. Most of the electron energy is dissipated in the form of heat but a small number of photons (X-rays) with peak energy equal to the attracting potential are produced.
  • the strong positive charge typically 50 kV
  • the transmission anode 13 needs to be very thin (typically half a wavelength, of the order of 5 ⁇ m) to allow the X-rays to exit.
  • a reflective anode (rather than a transmission anode) can be used with a radiation transparent window in the otherwise radiopaque rod 12 providing an exit path for the X-ray beam.
  • the radiation is directed to the cancerous tissue, normally at a distance of 20-50 mm from the anode 13.
  • the extent to which electrons emitted by the filament 11 can be effectively focussed is limited because of the non-uniform shape of the coiled wire filament. Poor focussing of the electrons reduces the quantity of useable X-ray radiation output by the tube and increases the risk of X-ray radiation being undesirably generated in other parts of the apparatus than the anode 13.
  • the tube can be relatively inefficient because so much of the electron energy is dissipated as heat. Either the tube has to be operated at low power (to allow the heat to dissipate) which undesirably increases treatment time, or a cooling mechanism for the anode needs to be provided such as that disclosed in US8094784 (Rapiscan Systems, Inc).
  • An X-ray tube needs to have very specific characteristics in order to be successfully used as radiotherapy apparatus for the treatment of human cancers.
  • radiotherapy apparatus for the treatment of human cancers.
  • radiotherapy apparatus as defined in claim 1. Further features of the invention are defined in the appended claims.
  • FIG 2 is a schematic illustration of radiotherapy apparatus having a vacuum chamber 20 containing a heating filament 21.
  • the heating filament 21 is used to heat an electron emissive cathode 22 comprising a generally cylindrical shape with a hemispherical end coated with an electron emissive material such as strontium. Electrons are emitted to produce an electron beam. In this way, the electrons used to produce the electron beam are emitted from an indirectly heated cathode rather than directly from the filament. Electrons emitted from the cathode 22 (the electron beam) are focussed along a desired path by a focus electrode 23.
  • the shape of the cathode 22 can be selected to optimise the profile of the electron beam so that it has a substantially circular profile.
  • the electron beam is attracted towards a rod-shaped anode structure or conduit 24 within the vacuum chamber 20, at the distal end of which it is focussed onto an anode (described in more detail below).
  • the rod is typically at least 10-15 cm long and preferably 20 cm in order to reach into body cavities such as rectum and vagina. It is desirable for the electron beam to enter the rod structure 24 centrally for it to reach the anode. Centering of the electron beam can be achieved by magnetic deflection. It is known to use electromagnets for this purpose but their performance is temperature dependant, they are relatively large, require control circuits, and it can be difficult to sense when they are working correctly.
  • FIG. 2 An alternative positioning apparatus for the electron beam is illustrated in Figure 2 in which an array of high field intensity permanent magnets 25 located near the proximal end of the rod 24 are position-adjustable. There are preferably three permanent magnets spaced with 120° separation around the longitudinal axis of the rod 24. The magnetic field intensity can be changed by advancing or retracting the magnets 25 radially in relation to the longitudinal axis of the rod.
  • a further advantage of the electron beam profile being symmetrical is that the effect of such magnetic positioning electrodes (and indeed the influence of the electrostatic focussing electrode 23) is uniform, permitting a relatively simple design thereof.
  • a "scraper" electrode assembly 26 comprising a non-radiation-emissive (low density) material, for example aluminium, is located at the point along the axis immediately forward (distal) of the deflecting magnets 25.
  • the scraper electrode has the effect of absorbing any electrons which are significantly misaligned that would, if not absorbed, produce unwanted and potentially dangerous X-ray radiation at the rod entrance.
  • the beam positioning apparatus and scraper electrode assembly may be useful in any radiotherapy apparatus having a rod-shaped electron beam conduit, not necessarily only such apparatus having an indirectly heated electron-emissive cathode.
  • the target anode 27 located at the end of the rod 24 is generally hemispherical. Incidence of the electron beam on the anode causes the emission of X-rays therefrom.
  • the anode 27 is preferably of the transmission type whereby X-rays are emitted from the assembly isotropically or in a spherical field due to the anode being sufficiently thin (less than 0.5 of the radiation wavelength) to avoid self-absorption.
  • the target anode 27 is deposited on a beryllium transmissive hemispherical window 28 to ensure good thermal conduction to a surface external to the vacuum chamber 20.
  • the curvature of the window 28 and hence the anode surface when combined with the large focal spot, eliminates lateral fall off which is normally associated with micro focus electron beams when they interact with a conventional planar perpendicular X-ray target anode.
  • the large diameter (preferably 4 mm) focal spot also has two further advantages:
  • a ceramic insulator 29 is located in the rod proximally of the anode 27 so that X-rays are emitted preferably from a 310° field rather than a 360° spherical field.
  • the features of the target anode described above may be useful in any radiotherapy apparatus having a rod-shaped electron beam conduit, not necessarily only such apparatus having an indirectly heated electron-emissive cathode.
  • Heat is generated at the distal end of the rod 24 and the proximal end at the vacuum chamber 20 must be maintained at near ambient temperature to avoid instability within the vacuum chamber 20. This temperature gradient (which may be in excess of 200 degrees Centigrade) can cause undesirable physical distortion of the rod 24.
  • Known cooling systems tend to be located at and for the purpose of cooling the anode only.
  • a cooling system comprising a jacket 30 closely surrounding substantially the whole rod 24.
  • the cooling jacket 30 contains a circulating coolant fluid (for example oil or water) which extracts heat to minimise temperature stresses on the rod.
  • cooling system may be useful in any radiotherapy apparatus having a rod-shaped electron beam conduit, not necessarily only such apparatus having an indirectly heated electron-emissive cathode.
  • the radiation output will be proportional to the electron beam current. This only holds true if the entire beam hits the target anode 27. It is, therefore, useful to monitor the current flow at the target window 28 rather than at the electron gun (i.e. filament 21/cathode 22).
  • the features of the radiation output monitor described above may be useful in any radiotherapy apparatus having a rod-shaped electron beam conduit, not necessarily only such apparatus having an indirectly heated electron-emissive cathode.
  • the radiotherapy apparatus of the present invention is capable of being used in association with a set of applicators of the type described in the inventors' co-pending application FR1153529 .
  • each applicator in the set comprises a spherical hollow head of different diameter having an outer surface adapted to be in contact with a cavity of living tissue and an inner surface defining an internal volume adapted to receive X-rays from the radiotherapy apparatus, wherein at least one zone of the head is capable of being traversed by said X-rays, and wherein the thickness of said zone is a function of the diameter of said head, configured so that the X-ray dose produced at the outer surface is between 18 and 22 Gray.
  • Radiotherapy apparatus as described herein is capable of delivering a therapeutic dose in less than three minutes to avoid error due to involuntary movement, discomfort or in the case of intra-operative treatment, undesirable increases in the procedure time.

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  • Physics & Mathematics (AREA)
  • Fluid Mechanics (AREA)
  • Radiation-Therapy Devices (AREA)

Claims (14)

  1. Appareil de radiothérapie, comprenant :
    une chambre à vide (20) dans laquelle est disposée une source d'électrons (22) apte à mettre un faisceau d'électrons ;
    une anode cible générant un rayonnement (27) apte à générer des rayons X en réponse à l'incidence du faisceau d'électrons sur celle-ci, l'anode (27) étant déposée sur une fenêtre hémisphérique (28) en béryllium ;
    un conduit en forme de tige (24) destiné à guider le faisceau d'électrons vers l'anode qui est située à son extrémité distale ; caractérisé en ce que :
    la source d'électrons (22) comprend une cathode à émission d'électrons chauffée indirectement ;
    un isolant (29) se trouve dans le conduit en forme de tige (24) à proximité de l'anode (27) de sorte que l'anode soit isolée électriquement ;
    la fenêtre (28) est couplée au conduit en forme de tige (24) par l'intermédiaire de l'isolant (29) ; et
    une résistance (R1) connecte électriquement la fenêtre (28) au conduit en forme de tige de sorte à créer un potentiel proportionnel au courant de faisceau.
  2. Appareil de radiothérapie selon la revendication 1, l'isolant (27) étant un isolant en céramique.
  3. Appareil de radiothérapie selon la revendication 1 ou 2, des rayons X étant émis dans un champ de 310° à partir d'un plan traversant l'axe longitudinal de l'appareil.
  4. Appareil de radiothérapie selon l'une quelconque des précédentes revendications comprenant en outre un système de refroidissement destiné à refroidir la surface du conduit en forme de tige (24) comprenant une chemise de refroidissement entourant sensiblement ladite tige, la chemise contenant du fluide de refroidissement.
  5. Appareil de radiothérapie selon la revendication 4, le fluide de refroidissement comprenant de l'huile ou de l'eau.
  6. Appareil de radiothérapie selon la revendication 4 ou 5, le liquide de refroidissement circulant au sein de ladite chemise de refroidissement.
  7. Appareil de radiothérapie selon l'une quelconque des revendications précédentes, l'anode étant généralement concave telle que vue de la cathode, de préférence généralement hémisphérique.
  8. Appareil de radiothérapie selon l'une quelconque des revendications précédentes, l'anode cible (27) étant plus grande en diamètre que le faisceau d'électrons, et éventuellement, l'anode cible (27) ayant un point focal sur lequel le faisceau d'électrons peut être centré, d'un diamètre de 4 mm.
  9. Appareil de radiothérapie selon l'une quelconque des revendications précédentes comprenant en outre un moyen de positionnement de faisceau d'électrons situé à l'extrémité proximale dudit conduit en forme de tige (24).
  10. Appareil de radiothérapie selon la revendication 9,
    le moyen de positionnement de faisceau comprenant des aimants permanents qui sont sélectivement mobiles radialement vers et à l'opposé de l'axe longitudinal dudit conduit en forme de tige (24), de préférence
    lesdits aimants permanents comprenant trois aimants permanents généralement disposés à intervalles réguliers autour de la circonférence dudit conduit en forme de tige (24).
  11. Appareil de radiothérapie selon l'une quelconque des revendications précédentes, comprenant en outre un ensemble d'électrodes de racleur comprenant un matériau non radioactif situé à l'extrémité proximale dudit conduit en forme de tige (24) pour absorber un faisceau d'électrons mal aligné.
  12. Appareil de radiothérapie selon l'une quelconque des revendications précédentes, comprenant en outre un moniteur de sortie de rayonnement, de préférence
    le moniteur de sortie de rayonnement comprenant ladite résistance pour permettre la surveillance du courant de faisceau d'électrons au niveau de l'anode.
  13. Appareil de radiothérapie selon l'une quelconque des revendications précédentes, l'appareil étant un dispositif de curiethérapie.
  14. Système de radiothérapie comprenant un appareil de radiothérapie selon l'une quelconque des revendications précédentes et un ensemble d'applicateurs, de préférence
    chaque applicateur comprenant une tête creuse sphérique de diamètre différent ayant une surface externe conçue pour être en contact avec une cavité de tissus vivants et une surface interne définissant un volume interne conçu pour recevoir des rayons X provenant dudit appareil de radiothérapie, au moins une zone de la tête pouvant être traversée par lesdits rayons X, et l'épaisseur de ladite zone étant fonction du diamètre de ladite tête, conçu de sorte que la dose de rayons X produits au niveau de la surface externe soit comprise entre 18 et 22 Gray.
EP13723919.0A 2012-05-16 2013-05-16 Appareil de radiothérapie Active EP2850634B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
GB1208631.0A GB2502109A (en) 2012-05-16 2012-05-16 X-ray radiotherapy apparatus with indirectly heated emissive cathode
PCT/GB2013/051257 WO2013171491A1 (fr) 2012-05-16 2013-05-16 Appareil de radiothérapie

Publications (2)

Publication Number Publication Date
EP2850634A1 EP2850634A1 (fr) 2015-03-25
EP2850634B1 true EP2850634B1 (fr) 2017-07-12

Family

ID=46458947

Family Applications (1)

Application Number Title Priority Date Filing Date
EP13723919.0A Active EP2850634B1 (fr) 2012-05-16 2013-05-16 Appareil de radiothérapie

Country Status (4)

Country Link
EP (1) EP2850634B1 (fr)
ES (1) ES2644288T3 (fr)
GB (1) GB2502109A (fr)
WO (1) WO2013171491A1 (fr)

Family Cites Families (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5165093A (en) * 1992-03-23 1992-11-17 The Titan Corporation Interstitial X-ray needle
US6463124B1 (en) * 1998-06-04 2002-10-08 X-Technologies, Ltd. Miniature energy transducer for emitting x-ray radiation including schottky cathode
US6319188B1 (en) * 1999-04-26 2001-11-20 Xoft Microtube, Inc. Vascular X-ray probe
US6493419B1 (en) * 2001-06-19 2002-12-10 Photoelectron Corporation Optically driven therapeutic radiation source having a spiral-shaped thermionic cathode
CN1596140A (zh) * 2001-06-19 2005-03-16 光电子公司 光学驱动治疗辐射源
US20020191746A1 (en) * 2001-06-19 2002-12-19 Mark Dinsmore X-ray source for materials analysis systems
US7127033B2 (en) * 2004-02-28 2006-10-24 Xoft, Inc. Miniature x-ray tube cooling system
US20060126789A1 (en) * 2004-12-10 2006-06-15 Carl Zeiss Stiftung Catheter with inflatable balloon assembly and optically activated x-ray source

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
None *

Also Published As

Publication number Publication date
ES2644288T3 (es) 2017-11-28
GB2502109A (en) 2013-11-20
GB201208631D0 (en) 2012-06-27
WO2013171491A1 (fr) 2013-11-21
EP2850634A1 (fr) 2015-03-25

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