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WO2000074105A1 - Tube a rayons x et catheter muni d'un tel tube - Google Patents

Tube a rayons x et catheter muni d'un tel tube Download PDF

Info

Publication number
WO2000074105A1
WO2000074105A1 PCT/DE2000/001790 DE0001790W WO0074105A1 WO 2000074105 A1 WO2000074105 A1 WO 2000074105A1 DE 0001790 W DE0001790 W DE 0001790W WO 0074105 A1 WO0074105 A1 WO 0074105A1
Authority
WO
WIPO (PCT)
Prior art keywords
ray tube
anode
catheter
ray
cathode
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.)
Ceased
Application number
PCT/DE2000/001790
Other languages
German (de)
English (en)
Inventor
Erich Hell
Mathias HÖRNIG
Manfred Pfeiler
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.)
Siemens AG
Siemens Corp
Original Assignee
Siemens AG
Siemens Corp
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Siemens AG, Siemens Corp filed Critical Siemens AG
Publication of WO2000074105A1 publication Critical patent/WO2000074105A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
    • A61N5/1002—Intraluminal radiation therapy
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00—X-ray tubes
    • H01J2235/08—Targets (anodes) and X-ray converters
    • H01J2235/086—Target geometry

Definitions

  • the invention relates to an X-ray tube with an anode and a cathode.
  • the invention also relates to a catheter provided for insertion into the human vascular system with such an x-ray tube.
  • PTCA percutaneous transluminal coronary angioplasty
  • the use of stents can somewhat reduce the number of cases in which restenosis forms: nevertheless, a treatment method which has allowed a significant further reduction in the formation of restenosis would achieve substantial benefits for the patient. namely, in addition to the avoidance of conventional and surgical follow-up interventions, even in a difficult starting situation, an extended stenosis-free interval and thus an improved quality of life.
  • Range of the high-energy radioactive radiation sources used are not to be carried out in the same clinical environment in which the PTCA takes place.
  • a catheter containing a miniaturized x-ray tube to perform radiation therapy of vascular wan ⁇ en with X-rays, as described in WO 97/07740 AI.
  • the X-ray quanta in the area of the central axis are drawn using electrons that are generated by field emission or the polarization of ferroelectrics. With field emission, there is a risk that the field emission current m of a microtip on the cathode will lead to evaporation and breakdown in a vacuum if a critical current density is exceeded.
  • the x-ray tubes described also have the disadvantage that the x-ray radiation emanates from a point source lying on the central axis of the x-ray tube, which is associated with a drop in the x-ray dose along the longitudinal axis of the x-ray tube.
  • part of the X-ray radiation is absorbed by the materials in the catheter.
  • the X-ray radiation loses intensity until it strikes the tissue tissue, since its point of origin is relatively far away from the tissue tissue and the intensity of the X-ray radiation is inversely proportional to the distance between the tissue tissue and the point of origin of the X-ray radiation.
  • an X-ray tube with a vacuum housing in which an elongated cathode and an anode surrounding it are accommodated, the anode having at least essentially linear sections which are arranged at a distance from one another, the linear sections of the Anode preferably in the manner of a network, in the manner of a cage or in the manner of a coil and according to a preferred embodiment form close to the wall of the vacuum housing, ie are at least closer to the wall of the vacuum housing than to the cathode.
  • the anode which is made of a material with a high atomic number, thus represents a non-closed envelope system surrounding the cathode, which allows the X-ray radiation to be generated close to the tissue to be treated, so that the X-ray radiation is on its way the vascular tissue to be treated loses little intensity.
  • the anode in the case of the X-ray tube according to the invention is not a transmission anode, but rather an anode composed of linear cut-offs. This is understood to mean “that the line-shaped sections have such a small width that only the smaller part of the envelope surface of the arode is formed by the line-shaped sections.
  • the line-shaped sections are less than 50%, but preferably a maximum of 10 - make out the envelope of the anode.
  • a catheter for insertion into the human vascular system which for treating vascular walls with X-rays contains at its distal end an X-ray tube of the type described above and which is preferably flexible for easier application
  • the catheter is provided in the region of the X-ray tube, but outside the main propagation path of the X-ray radiation emanating from the anode, with several inflatable balloons arranged at angular intervals, which are dimensioned such that when the catheter is inserted into a vessel, between adjacent inflated balloons a flow path for blood remains free.
  • the protein of the blood is prevented from curdling because of the not inconsiderable outside temperature of the catheter, since at least a reduced blood flow takes place through the flow paths located between adjacent inflated balloons.
  • Fig. 1 shows an inventive X-ray tube m schematic, partially block diagram-like representation in longitudinal section as part of an inventive
  • FIG. 2 shows a cross section through the catheter according to FIG. 1,
  • FIG. 3 shows a further exemplary embodiment in a representation analogous to FIG. 1, Fig. 4, the anode of the X-ray tube shown in FIG. 3 m Perspecti ⁇ vischer representation, and
  • the x-ray tube according to the invention designated overall by 1 in FIG. 1, has, according to FIG. 1, a vacuum housing 2, preferably of at least substantially rotationally symmetrical design, of lenticular shape, which has an outer diameter of, for example, 4 mm and is made of an X-ray-transparent material with a low atomic number, for example boron nitride or titanium.
  • An elongated thermal cathode designated as a whole by 3, is inserted into the vacuum housing 2 and has a length of e.g. 1 to 10 mm and the longitudinal axis of which at least approximately coincides with the longitudinal axis of the vacuum housing 2 and thus the longitudinal axis of the X-ray tube.
  • the two connections of the cathode 3 are led to the outside in a vacuum-tight manner by insulators from the vacuum housing 2.
  • a straight filament for example made of tungsten
  • cathode 3 a straight filament, for example made of tungsten
  • an elongated glow cathode can also be provided within the scope of the invention.
  • An anode 4 made of an X-ray-emissive anode material with a high atomic number is provided inside the vacuum housing 2, which surrounds the cathode 3 on all sides and is supported in that it rests on the inside of the vacuum housing 2, whereby the vacuum housing 2 assumes the same potential as the anode 4.
  • the anode 4 has at least essentially line-shaped sections which are arranged at a distance from one another, 1 in the case of the exemplary embodiment according to FIG. 1, the individual windings of a coil which is preferably circular in cross section and which is cylindrical in the case of the exemplary embodiment described are cylindrical. Since the diameter of the wire is small compared to the distance between adjacent turns of the coil, for example a ratio of 1: 3, the major part of the envelope surface of the anode 4 is free of anode material. The distance that the turns of the filament are from the inside of the vacuum housing is significantly less than their distance from the cathode 3.
  • a high-voltage generator 5 is provided, which is connected to the x-ray tube 1 via a taxial cable 6.
  • the triaxial cable 6 has a monofilament inner conductor 7, which is surrounded by high-voltage insulation 8, which separates it from a center conductor 9, which is known per se as a wire mesh or a helically wound foil strip.
  • the center conductor 9 is also surrounded by high-voltage insulation 10, which separates it from an outer conductor 11, which is likewise designed in a manner known per se as a wire mesh or a helically wound foil strip.
  • the X-ray tube 2 is embedded in a high-voltage insulation, X-ray-transparent insulating material body 12, which is formed from a suitable X-ray-transparent material.
  • the X-ray tube 1 forms a catheter K with the triaxial cable 6 and the insulating body 12, which catheter K is made of a biocompatible, i.e. physiologically well-tolerated material, e.g. Silicone, is coated.
  • catheter K is made of a biocompatible, i.e. physiologically well-tolerated material, e.g. Silicone, is coated.
  • the Isolierstoffkorper 12 is completely surrounded by the outer conductor 11 of the T ⁇ axialtent 6, which for safety of the patient is connected to a protective potential 9, since the tube tension is of the order of 20 kV, corresponding to an average energy of the X-ray quanta of 10 keV, and the catheter may end up in the patient's heart.
  • the X-ray tube 1 is thereby subjected to high voltage, i.e. with the tube voltage, applied that a pole of the high voltage generator 5 via the inner conductor 7 of the T ⁇ axialkul 6 with one connection of the cathode 3 and the other pole of the high voltage generator 5 via the central conductor 9 of the triaxial cable 6 with the anode 3, which for this purpose has a vacuum-tight connection led out of the vacuum housing 2 through one of the insulators.
  • the heating current required for the operation of the X-ray tube 1 for the cathode 3 is superimposed on the tube voltage, which is a DC voltage, as a preferably high-frequency AC voltage.
  • a modulator 14 is connected to the high-voltage generator 5.
  • the anode 4 is connected to the second connection of the cathode 3 via a capacitor 15.
  • the capacitor 15 prevents a direct current flowing through it between the anode 4 and the cathode 3, but, on the other hand, is dimensioned taking into account the frequency at which the modulator 14 operates so that it allows the flow of the heating current through the cathode 3 .
  • the cathode 3 During operation of the X-ray tube 1, the cathode 3 thus emits electrons over its entire length, which due to the electric field between the anode 4 and the cathode 3 are accelerated outwards in all directions and hit the line-shaped sections of the anode 4 and X-rays Draw (brake radiation) that emerges from the vacuum housing 2 of the X-ray tube 1 to the outside. Due to the use of an elongated cathode 3 on its Whole length is surrounded by the anode 4, the length of the cathode 3 and thus the longitudinal axis of the x-ray tube 1 result in an at least substantially uniform intensity distribution of the x-ray radiation, which is advantageous for the treatment of vessel walls.
  • the X-rays emanating from the anode 4 lose little intensity on their way to the tissue to be treated. Also due to the presence of the anode 4, there is no significant weakening of the intensity of the X-radiation, since, due to the fact that the anode 4 consists of linear sections, unlike in the case of a transmission anode, there is practically no weakening of the emitted X-rays by the anode 4 itself.
  • the catheter m shown in FIG. 1 has several, for example three, inflatable balloons 16 which are located close to the X-ray tube 1, if necessary, also shortly behind the X-ray tube 1, outside the main direction of propagation of the X-ray radiation emanating from the X-ray tube 1 on the lateral surface of the catheter, m offset at angular intervals.
  • the balloons 16 can be inflated via m channels not shown in the figures and, with a length of, for example, 2 to 4 mm, their cross-section m from FIG.
  • each of the balloons 16 extends over a range of approximately 60 °, so that a flow path remains free between adjacent balloons 16, which also extends over a range of approximately 60 °.
  • 3 and 4 differs from that previously described first in that the triaxial cable has a bifilar inner conductor with the two conductors 18a and 18b, which are connected to the two connections of the cathode 3, which in the case of the 3 and 4 is designed as a U-shaped curved glow wire.
  • a heating voltage generator 19, which is provided in addition to the high-voltage generator 5, is connected in a conventional manner to the other ends of the conductors 18a and 18b.
  • the negative pole of the high-voltage generator 5 is also connected to the conductor 18a.
  • the anode 4 m surrounding the cathode 3 m is designed as a cage which consists of a number of circular, line-shaped sections 20 and is composed of straight line-shaped sections 21, for example by welding, the sections 20 and 21 being formed from wire, preferably a circular cross section, m only a circular section and a straight section with the corresponding reference number in FIGS. 3 and 4 veins
  • FIG. 5 shows a further exemplary embodiment, which differs from the previously described plane in that the line-shaped sections of the anode 4 are wires, preferably circular in cross-section, which are connected to one another in the manner of a network, of which the m of FIG. 5 visible with the reference numerals 22 to 27.
  • the X-ray tube does not have to be accommodated in an insulating body 12, as in the case of the previously described exemplary embodiments, that of the outer conductor 11 and an outer skin 13 is surrounded. Rather, the vacuum housing of the X-ray tube can be formed from a biocompatible material, for example glass-like carbon, as it is sold under the name Sigradur®.
  • the outer skin 13 can be made removable. It is then possible to remove the outer skin 13 after use of the catheter and to replace it with a fresh, sterile outer skin 13, as a result of which the catheter is ready for use again.

Landscapes

  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Pathology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Radiation-Therapy Devices (AREA)

Abstract

L'invention concerne un tube à rayons X (1) comprenant un boîtier à vide (2) dans lequel sont disposées une cathode longitudinale (3) et une anode (4) entourant la cathode, caractérisé en ce que l'anode (4) présente au moins des sections sensiblement linéaires disposées à distance l'une de l'autre, et en ce que les sections linéaires de l'anode (4) sont disposées à la manière d'un treillis, d'une cage ou d'une hélice, à proximité immédiate de la paroi du boîtier à vide (2).
PCT/DE2000/001790 1999-06-02 2000-05-31 Tube a rayons x et catheter muni d'un tel tube Ceased WO2000074105A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE1999125456 DE19925456B4 (de) 1999-06-02 1999-06-02 Röntgenröhre und Katheter mit einer solchen Röntgenröhre
DE19925456.7 1999-06-02

Publications (1)

Publication Number Publication Date
WO2000074105A1 true WO2000074105A1 (fr) 2000-12-07

Family

ID=7910134

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/DE2000/001790 Ceased WO2000074105A1 (fr) 1999-06-02 2000-05-31 Tube a rayons x et catheter muni d'un tel tube

Country Status (2)

Country Link
DE (1) DE19925456B4 (fr)
WO (1) WO2000074105A1 (fr)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6718012B2 (en) * 2002-05-30 2004-04-06 Moshe Ein-Gal Electromagnetic wave energy emitter

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB357978A (en) * 1930-06-30 1931-09-30 Frederick Alexander Lindemann Improvements in x-ray tubes
DE1064649B (de) * 1956-04-07 1959-09-03 Licentia Gmbh Membrananodenroentgenroehre
DE2358512A1 (de) * 1973-11-23 1975-06-05 Siemens Ag Verfahren zur herstellung von roentgenroehren-anoden
DE2421119A1 (de) * 1974-05-02 1975-11-13 Burns Stephen J Roentgenroehre
FR2534066A1 (fr) * 1982-10-05 1984-04-06 Thomson Csf Tube a rayons x produisant un faisceau a haut rendement, notamment en forme de pinceau
EP0187020A2 (fr) * 1984-12-20 1986-07-09 Varian Associates, Inc. Source de rayons X de grande intensité
USRE34421E (en) * 1990-11-21 1993-10-26 Parker William J X-ray micro-tube and method of use in radiation oncology
WO1997007740A1 (fr) * 1995-08-24 1997-03-06 Interventional Innovations Corporation Catheter a rayons x

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US34421A (en) * 1862-02-18 Improvement in channeling-tools for harness-makers

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB357978A (en) * 1930-06-30 1931-09-30 Frederick Alexander Lindemann Improvements in x-ray tubes
DE1064649B (de) * 1956-04-07 1959-09-03 Licentia Gmbh Membrananodenroentgenroehre
DE2358512A1 (de) * 1973-11-23 1975-06-05 Siemens Ag Verfahren zur herstellung von roentgenroehren-anoden
DE2421119A1 (de) * 1974-05-02 1975-11-13 Burns Stephen J Roentgenroehre
FR2534066A1 (fr) * 1982-10-05 1984-04-06 Thomson Csf Tube a rayons x produisant un faisceau a haut rendement, notamment en forme de pinceau
EP0187020A2 (fr) * 1984-12-20 1986-07-09 Varian Associates, Inc. Source de rayons X de grande intensité
USRE34421E (en) * 1990-11-21 1993-10-26 Parker William J X-ray micro-tube and method of use in radiation oncology
WO1997007740A1 (fr) * 1995-08-24 1997-03-06 Interventional Innovations Corporation Catheter a rayons x

Also Published As

Publication number Publication date
DE19925456A1 (de) 2000-12-14
DE19925456B4 (de) 2004-11-04

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