WO1992009998A1 - X-ray micro-tube and method of use in radiation oncology - Google Patents
X-ray micro-tube and method of use in radiation oncology Download PDFInfo
- Publication number
- WO1992009998A1 WO1992009998A1 PCT/US1991/007907 US9107907W WO9209998A1 WO 1992009998 A1 WO1992009998 A1 WO 1992009998A1 US 9107907 W US9107907 W US 9107907W WO 9209998 A1 WO9209998 A1 WO 9209998A1
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- WO
- WIPO (PCT)
- Prior art keywords
- tube
- ray
- glass
- tumor
- patient
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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
-
- 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
Definitions
- This invention relates to the production and medical use of X-rays, and more particularly to the production, by X-ray micro-tubes, of low energy, highly absorbable, polychromatic X-rays and to the use of those X-rays in the treatment of tumors when such X-ray micro-tubes are placed within, or adjacent to, mammalian bodies in very close proximity to, or within, tumors.
- the goal of radiation therapy is to achieve in a selected treatment volume, a dose distribution of radiation that provides the patient with maximum tumor control and the
- the radioisotopes may be placed in large external machines such as a '"Cobalt teletherapy machine, or implanted near a tumor site.
- a '"Cobalt teletherapy machine or implanted near a tumor site.
- Present Applicants are aware of a surgical procedure being utilized in the treatment of brain tumors in which tiny holes are drilled in the skull. The surgeon inserts thin tubes with closed bottom ends into the tumor. Radioactive pellets the size of peas are inserted into the tubes. The implants deliver strong radiation to the tumor. They are removed a few days later.
- the high energy devices have been designed to produce a maximum of antitumor activity with a minimal effect on a patient's normal tissues, the side effects of the radiation therapy on the patient's normal tissue can still be the limiting factor in a course of therapy.
- the McCrary X-ray tube has a needle cathode along the axis of the tube and an exit window at the end behind the cathode or optimum X-ray output.
- the present invention is a method and apparatus for treating tumors by low energy, highly absorbable, polychromatic X-rays (also called Bremsstrahlung or White radiation) produced by small X-ray micro-tubes placed within, or adjacent to, a patient's body in close proximity to, or within, a tumor.
- the design of the X-ray micro-tube can be relatively simple: a miniature X-ray production source, generally a glass tube a fraction of an inch in diameter and with a length of approximately one- half of an inch (approximately 127 centimeters), to several inches, containing at least an anode and a cathode.
- the cathode may be a pointed cold cathode, or a heated filament, and the tube must be evacuated to, at most, 10 "6 Ton * .
- the target portion of the anode may be formed of tungsten, as in conventional X-Ray tubes.
- the glass tube may be surrounded by a plastic envelope so as to prevent injury to the patient or health professional should the glass break.
- a metal jacket containing a window may be placed around the tube so as to allow the X-rays to travel only in the direction of the tumor.
- the X-ray micro-tube may be disposable or re-sterilized.
- the depth of X-ray penetration into tissues can be easily and accurately controlled by adjusting the voltage applied to the X-ray micro-tube. Tissue penetration depths within a few centimeters from the surface of the tube are characteristic of the White radiation produced by the micro-tubes. This reduces damage to normal tissue except in the immediate vicinity of the tumor.
- the X-rays are produced by applied voltages between 10 kilovolts and 60 kilovolts.
- the voltage applied to the X-ray micro-tube may have an operable frequency between direct current and 1,000,000 cycles per second, the higher frequencies providing greater patient safety.
- the current through the X-ray micro-tube is generally much lower than that conventionally used and is in the micro-ampere range. Patient safety is assured by ground fault interrupters and current limiting circuitry. f?
- micro-X-ray tubes may be placed in-situ by a number of methods, including, but not
- 5 limited to: implantation during surgery; insertion through a normal body orifice: insertion in conjunction with a fiber-optic scope through a normal body orifice; in conjunction with a fiber-optic scope through a surgical incision; insertion through a trocar catheter; or insertion through a catheter contained within a surgical incision.
- Figure 1 is a graph of Mass Absorption Coefficient, ⁇ /p, versus Energy, MeV, showing the ranges for Photoelectric and Compton Scattering absorption.
- Figure 2 is a graph illustrating the spectral distribution of the X-ray energies and relative intensities emitted from a tungsten anode for various constant d.c. potentials.
- Figure 3 is a graph illustrating examples of Penetration-depth curves of constant d.c. voltage. KeV vs penetration depth in body tissue, in centimeters, for monochromatic X-rays, showing distance 25 for percentage of intensity remaining.
- Figure 4 includes schematic curves showing the changes in the intensity distribution of the White radiation spectrum from a tungsten anode at 50 KeV constant potential d.c. after penetrating through various depths of tissue.
- Figure 5 includes schematic curves showing the changes in the intensity distribution of the White radiation spectrum from a tungsten anode at 40 KeV constant potential d.c. after penetrating through various depths of tissue.
- Figure 6 includes schematic curves showing the changes in the intensity distribution of the
- Figure 7 includes schematic curves showing the changes in the intensity distribution of the White radiation spectrum from a tungsten anode at 25 KeV constant potential d.c. after penetrating through various depths of tissue.
- Figure 8A to 8J illustrate short X-ray micro-tube designs.
- Figure 8A illustrates a short micro-tube with a heated filament cathode.
- Figure 8B illustrates a short micro-tube with a cold cathode electron emitter.
- Figure 8C illustrates a very short micro-tube having the cathode and anode positioned on the same end, with an internal glass tube for insulating the anode connecting wire.
- Figures 8D(a) and 8D(b) illustrate the use of a thin internal anode film on the inside of the glass tube through which X-rays can penetrate to produce a cylindrical transmitted X-ray beam.
- Figures 8E(a) and 8E(b) illustrate the use of a thick internal anode film on the inside of the glass tube, the resulting back-scattered X-ray beam producing a hemicylindrical X-ray pattern.
- Figures 8F(a) and 8F(b) illustrate the use of a thin internal anode film on the inside of the glass tube resulting in a hemicylindrical transmitted X-ray pattern.
- Figure 8G illustrates a short micro-tube with a spot-type anode (thick or thin).
- Figures 8H(a) and 8H(b) illustrate the use of a thin internal hemispherical anode film used to produce a hemispherical X-ray pattern.
- Figure 9 illustrates a long micro-tube design with an enlarged end for evacuation and sealing.
- Figure 10 is a schematic illustration of a short liquid-cooled microtube assembly.
- Figure 11 is a schematic illustration of a short metal-jacketed microtube assembly.
- Electromagnetic radiation extends over a very wide range of wave lengths, i.e. from radio waves (3X10 4 m to 5m). microwaves (5X10 "2 m to lX10 " *m). infrared (lXlO ⁇ m to 7X10 7 m). visible (7X10 '7 m to 4X10 7 m), ultra-violet (4X10 _7 m to lX10 "8 m). X-rays and gamma rays (lX10 "8 m to lX10 "1 m).
- the wave lengths of X-rays are frequently expressed in angstroms (A) with 1A being equal to 10 "8 cm. These selected wave length bands of radiation have been classified as ranges which interact with matter in familiar ways.
- the value of the wavelength determines the size of an object with which the electromagnetic radiation will react. Radio waves will react with large electrical conductors, visible and ultra-violet light react with the outer shell electrons in atoms, and X-rays interact with the innermost orbital electrons. The shorter the wavelength the higher the energy of the radiation.
- the reciprocal of the wavelength is the frequency, with the wavelength commonly being represented by the symbol ⁇ , and the frequency by the Greek letter v.
- the energy, E. is equal to ⁇ v, where * h is Planck's constant.
- the nature and properties of the radiation within the X-ray band vary with the energy (or wavelength) of the X-ray, just as the characteristics of the light in the visible range vary with the wave length of the radiation, the shorter wave lengths appearing as blue colors and the longer ones as orange-red colors.
- a brief discussion of how the different wave lengths of X-rays are produced and how they differ in their interactions with body tissues provides an understanding of the uniqueness and value of the present invention.
- Medically useful X-rays are normally produced in evacuated tubes (usually made of glass) containing two elements, a cathode and an anode.
- the cathode is typically a tungsten filament that is heated to a temperature sufficiently high to cause electrons to reach velocities permitting them to escape from the filament.
- the escaping electrons are attracted to the anode at the opposite end of the tube (also typically formed of tungsten), which exists at a high positive potential, commonly in the range of 50.000 to 2 million volts.
- the electrons are accelerated during their passage toward the anode, reaching a high velocity before collid ng with the anode and causing inner shell electrons to be ejected from the tungsten atoms.
- the energy gained by the participating electrons is measured in electron volts (eV) where e is the electrical charge of the electron and V is the voltage difference between the cathode and the anode.
- eV electron volts
- Photoelectric Absorption is the dominant form of X-ray absorption only in the lowest range of X-rays (e.g. 10 to 60 kilovolts). It occurs when the energy of the X-ray photons is equal to the energy binding the innermost shell electrons of the atoms in the exposed matter. In this case, the X-ray photons interact with the electrons orbiting closest to the nucleus, causing them to be ejected from the atoms, and causing the photons to loose all of their energy and disappear. This reaction cannot occur at X-ray beam energies below the electron-atom binding energy. It is a maximum when the two energies are equal, and decreases rapidly with increasing X-ray energy above the maximum value.
- Absorption of higher energy X-ray radiation occurs almost entirely by Compton Scattering.
- This process involves the interactions of X-ray photons with any of the electrons in the cloud surrounding the nucleus of the interacting atom.
- an incident photon loses only part of its energy when it reacts with an electron, which acquires the energy lost by the photon and is ejected from the electron cloud of the- atom.
- the resulting photon with diminished energy is scattered and moves orward at some angle to the line of the incident beam.
- the energy of the scattered photon is not absorbed locally within the exposed material during this event, but the energy acquired by the participating electron is completely absorbed within the material.
- the energy change of the incident X-ray beam is divided into two parts, only one of which is directly absorbed.
- the effective absorption coefficient for a beam consisting of a broad spectrum of X-rays is the fraction of the beam that is absorbed during the passage of the beam through one centimeter of material and is composed of two parts: one being the component contributed by Photoelectric Absorption, and the other being due to the Compton effect.
- Figure 3 shows examples of approximate depth of penetration curves (Le. the distance through material which causes a specific decrease in the X-ray intensity to, for example, 1/2, 1/4, 1/10 etc. of the initial beam intensity. I is the intensity, while IQ refers to the initial intensity.)
- the values shown in this figure are for monochromatic radiation.
- the absorption coefficient is relatively constant.
- both the absorption coefficient and the X-ray intensity are strongly dependent upon the energy of the photons involved.
- the mass absorption coefficient for tissue varies from about 033 for 37 KeV to 33 at 12 KeV.
- Figures 4, 5, 6, and 7 show intensity decreases in the initial intensity values for white radiation from a tungsten anode X-ray tube at different tube potentials, as the beam penetrates into tissue.
- the shape of the Relative Intensity versus Energy (KeV) curve changes as the distance from the outer surface of the tissue being penetrated is increased.
- the absorption coefficient differs, as shown in Figure 1, with a much higher fraction of the lower X-ray energy components of the white radiation beam being absorbed than is the case for the higher energy components.
- the curves in Figure 4 illustrate this effect at various depths in tissue.
- Figure 4 illustrates examples of the nature of the changes that occur at a high energy value within the 50 KeV generated white radiation spectrum, to those of a low energy value of the same spectrum, by comparing initial intensities on the I 0 curve to intensities on the same depth in tissue curve.
- the high energy case be chosen as 42 KeV and the low energy be selected as 20 KeV.
- I ⁇ 5.5 (from Figure 4)
- ⁇ 032 (from Figure 1)
- x 1cm.
- Figures 5-7 are generated in the same manner as Figure 4 but for constant potential d.c. voltages of 40 KeV, 30 KeV, and 25 KeV, respectively. Information of this kind is necessary for determining suitable voltages for treating tumors of different varieties and sizes while minimizing damage to nearby tissues.
- the micro-tubes are similar in principle to standard X-ray tubes except that they are much smaller and require only a small fraction of the tube current required in conventional commercial machines (i.e. microamperes vs milliamperes).
- the physical size of a tube can be a fraction of an inch in diameter and with a length as small as one-half of an inch, to as long as several inches. A variety of useful tube designs is possible.
- FIG. 8a a schematic illustration of an embodiment having a filament cathode is shown, designated generally as 20.
- An evacuated glass tube 22 contains a stable vacuum of at most 10 "6 Torr.
- a heated filament cathode 24 preferably a small tungsten filament
- an anode 26 are provided which are connected to an appropriate power source (as will be discussed below).
- the anode 26 can be made of any one of a number of different metals typically used, but tungsten is preferred (as it is in conventional commercial tubes).
- Tube 28 is a cold emission (or field emission) cathode tube (which has no filament).
- the electrons are emitted from a sharply pointed electrode 30, preferably formed of tungsten.
- a very high potential gradient develops between the sharply pointed tip of the electrode and the anode 32 when a high voltage is applied across the X-ray tube 28.
- use of a cold electron emitter tube has some advantages. This type of tube is simpler to make in smaller sizes than the heated filament type.
- the depth of penetration of the present X-ray microtubes can be easily controlled by varying the tube voltage.
- the total desired radiation exposure can be controlled by selecting an appropriate time of exposure.
- a great advantage of the micro-tube is that it can be placed on or very near the surface of the tumor, or within the tumor, so that radiation damage to normal tissue is minimized.
- the source to tumor distance for the micro-tubes therefore, is extremely small compared with the source to skin distance (SSD) of 20 to 50 centimeters with the X-ray units now in common use. Since the intensity of the X-ray beam varies inversely with the square of the distance from the beam source, for a given tube voltage, the same effective intensity of the X-ray beam at the site of a tumor can be produced by the micro-tube with about one one-thousandth of the current required for the proper operation of a large external tube. Therefore, the present invention operates in the low microampere range, rather than the low milliampere range required for currently used large tubes.
- Micro-tubes are relatively inexpensive and may be manufactured to be re-sterilized or disposable.
- the exterior surface of the tube is preferably covered with a thin tough biocompatible plastic material, as will be described below, to guard against damage to handlers or patients should accidental breakage of the glass tube occur.
- the plastic tube cover can also have a built-in water coolant jacket to dissipate the small amount of heat generated by the tube (operating at a small fraction of a watt).
- the power supply required is relatively simple and inexpensive because of the low current required (microamperes vs conventionally used milliamperes) and because of the relatively low tube voltages required (generally less than 60 kilovolts compared 60 kilovolts to one million volts for conventional equipment). Aside from the micro-tube itself, only state of the art equipment is necessary. However, one difference in detail is necessary. Conventional 60 cycle a.c. destroys the many normal nerve functions.
- the inventive concepts of the present invention provide for use of a frequency that would be sufficiently high so that the normal nerve functions of the body would not be affected if an inadvertent contact of the high voltage lead with body tissue did occur.
- Figure 8C illustrates the placement of the anode 34 and the cathode 36 on the same side of a micro-tube 38 to accomplish a reduced length.
- An internal glass tube 40 is used to support the anode 34 and to insulate the anode connecting wire 42.
- micro-tubes of the present invention may be manufactured in a variety of different ways to optimize their use.
- a glass micro-tube 42 is illustrated with a thin internal anode film 44 formed on its inner surface (preferably vacuum deposited tungsten).
- An axialiy extending filament cathode 46 is provided.
- a cylindrical X-ray pattern illustrated by the arrows 48 in Figure 8D(b) results. This design is particularly useful if the micro-tube is desired to be inserted near the center of the tumor.
- Figures 8E(a) and 8E(b) illustrate a relatively thick film anode 50 deposited or otherwise formed on portions of the inside of the glass tube 52. This results in a backscattered X-ray beam which produces a hemicylindrical X-ray pattern, as illustrated by arrows 54. The X-ray pattern is established at portions of the micro-tube which do not have the thick film formed thereon.
- a thin anode film 56 is formed on only a portion of the micro-tube 58. This results in a hemicylindrical X-ray pattern 60.
- An alternate anode design is illustrated in Figure 8G, the micro-tube being designated as 62. In this instance, the anode 64 is a spot type of thin or thick film.
- a hemispherical X-ray pattern 66 results from formation of an anode film 68 near the end of the micro-tube 70.
- the short micro-tubes illustrated in Figures 8A-8H are typically from one-fourth inch (approximately .635 cm) to two inches (approximately 5.08 cm) in length, preferably approx. 1/2" (approximately 127cm). Diameters may range from 1/8" to 1" (318cm to 234cm), preferably 1/4" (.635 cm).
- these micro-tubes may be placed in-situ by a number of methods, including, implantation during surgery; insertion through a normal body orifice; insertion in conjunction with a fiber-optic scope through a normal body orifice; insertion in conjunction with a fiber-optic scope through a surgical incision; insertion through a trocar catheter: or insertion through a catheter contained within a surgical incision.
- the micro-tubes may also be placed adjacent to the body next to the skin.
- Longer micro-tubes may alternately be used which may be up to several inches (Le. 2"-8" or 5.08cm-2032cm) in length.
- Figure 9 illustrates a schematic of a design of such a long micro-tube 72.
- the lead wire 74 for the cathode 76 and the lead wire 78 for the anode 80 connect to a power supply (not shown).
- Long micro-tube 72 is particularly useful in the brain and is made thin, for example, in the range of 1/8" to 1/4" (318cm to .635cm) in diameter.
- End 82 is enlarged and extends outside of the body, serving as a "compass" for accurately rotating the micro-tube and directing the X-rays in the desired manner.
- Liquid-cooled micro-tube assembly 84 includes a filament cathode 86 supported by a filament support structure 88 within an evacuated glass tube 90. Similarly, an anode 92 is supported by another filament support structure 94 within the evacuated glass tube 90. Glass tube 90 may be formed as described in the above-discussion regarding Figs 8 and 9. Glass tube 90 is positioned within a liquid coolant chamber % which is supplied by coolant hoses 98,100.
- Coolant chamber 96 is, in turn, enclosed within the main housing 102 of the micro-tube assembly 84. Housing 102 is preferably formed of plastic. Filament lead wires 104,106, anode lead wire 108, and coolant hoses 98,100, extend through the main housing 102. These five elements are preferably radially spaced and separated by walls to confine any leaks to a specific portion of the assembly. Dashed lines 110 schematically illustrate these walls. Additionally, approximately water seals 112 are provided.
- a metal-jacketed micro-tube assembly designated generally as 114, is illustrated in Figure 11.
- Assembly 114 includes a cathode 116 supported by a cathode support structure 118 within an evacuated glass tube 120.
- an anode 122 is supported by another support structure 124 within the evacuated glass tube 120.
- Glass tube 120 is contained within a metal jacket 126.
- Tube 120 may be formed as described in the above-discussion regarding Figs.8 and 9.
- a window 128 is provided in the metal jacket 126 for directing the radiation in the desired manner.
- Anode and cathode cables 130,132 including lead wires are provided for attachment to an external power source (not shown).
- the power supply needed for X-ray micro-tube operation is unique in that it is a low energy device that can be made easily portable and is less costly to make than those now supplied with deep therapy equipment, which require much higher levels of energy.
- Modern electronic designs and equipment capable of providing the currents and voltages needed for the operation of the micro-tubes are state of the art, and a variety of designs are available.
- Another essential feature of the invention is that the power supply circuit must contain a rapidly acting safety circuit interrupter that will immediately operate should anything happen to cause the tube current to suddenly increase to, for example, one milliampere, which is still very safe for a patient but undesirable for micro-tube operation.
Abstract
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Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
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JP4500815A JPH06502559A (en) | 1990-11-21 | 1991-10-25 | X-ray microtubes and methods used in radiation oncology |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US07/616,397 US5090043A (en) | 1990-11-21 | 1990-11-21 | X-ray micro-tube and method of use in radiation oncology |
US616,397 | 1990-11-21 |
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WO1992009998A1 true WO1992009998A1 (en) | 1992-06-11 |
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Application Number | Title | Priority Date | Filing Date |
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PCT/US1991/007907 WO1992009998A1 (en) | 1990-11-21 | 1991-10-25 | X-ray micro-tube and method of use in radiation oncology |
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US (2) | US5090043A (en) |
EP (1) | EP0560906A1 (en) |
JP (1) | JPH06502559A (en) |
WO (1) | WO1992009998A1 (en) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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EP0630038A1 (en) * | 1993-06-18 | 1994-12-21 | Hamamatsu Photonics K.K. | X-ray generation tube |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5369679A (en) * | 1990-09-05 | 1994-11-29 | Photoelectron Corporation | Low power x-ray source with implantable probe for treatment of brain tumors |
US5452720A (en) * | 1990-09-05 | 1995-09-26 | Photoelectron Corporation | Method for treating brain tumors |
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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 |
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US5653683A (en) * | 1995-02-28 | 1997-08-05 | D'andrea; Mark A. | Intracavitary catheter for use in therapeutic radiation procedures |
US5630426A (en) * | 1995-03-03 | 1997-05-20 | Neovision Corporation | Apparatus and method for characterization and treatment of tumors |
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US6377846B1 (en) | 1997-02-21 | 2002-04-23 | Medtronic Ave, Inc. | Device for delivering localized x-ray radiation and method of manufacture |
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US7338487B2 (en) * | 1995-08-24 | 2008-03-04 | Medtronic Vascular, Inc. | Device for delivering localized x-ray radiation and method of manufacture |
US5729583A (en) * | 1995-09-29 | 1998-03-17 | The United States Of America As Represented By The Secretary Of Commerce | Miniature x-ray source |
US20010003800A1 (en) * | 1996-11-21 | 2001-06-14 | Steven J. Frank | Interventional photonic energy emitter system |
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US5984853A (en) | 1997-02-25 | 1999-11-16 | Radi Medical Systems Ab | Miniaturized source of ionizing radiation and method of delivering same |
WO1998048899A2 (en) * | 1997-04-28 | 1998-11-05 | Newton Scientific, Inc. | Miniature x-ray unit |
US5854822A (en) * | 1997-07-25 | 1998-12-29 | Xrt Corp. | Miniature x-ray device having cold cathode |
EP1005702A1 (en) * | 1997-08-18 | 2000-06-07 | XRT Corp. | Cathode from getter material |
US6108402A (en) * | 1998-01-16 | 2000-08-22 | Medtronic Ave, Inc. | Diamond vacuum housing for miniature x-ray device |
AU2987699A (en) * | 1998-03-06 | 1999-09-20 | Xrt Corp. | Method and x-ray device using adaptable power source |
US6069938A (en) * | 1998-03-06 | 2000-05-30 | Chornenky; Victor Ivan | Method and x-ray device using pulse high voltage source |
US6036631A (en) * | 1998-03-09 | 2000-03-14 | Urologix, Inc. | Device and method for intracavitary cancer treatment |
US6463124B1 (en) | 1998-06-04 | 2002-10-08 | X-Technologies, Ltd. | Miniature energy transducer for emitting x-ray radiation including schottky cathode |
US6324257B1 (en) | 1998-06-04 | 2001-11-27 | X-Technologies Inc. | Radiotherapeutical device and use thereof |
DE19825563C1 (en) * | 1998-06-08 | 1999-12-02 | Siemens Ag | Catheter X=ray tube |
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DE19842466C2 (en) * | 1998-09-16 | 2000-07-13 | Siemens Ag | Power supply for a miniaturized X-ray tube |
US6134300A (en) * | 1998-11-05 | 2000-10-17 | The Regents Of The University Of California | Miniature x-ray source |
US6245047B1 (en) * | 1998-12-10 | 2001-06-12 | Photoelectron Corporation | X-Ray probe sheath apparatus |
EP1145271A1 (en) * | 1999-01-18 | 2001-10-17 | The Wahoo Trust | High energy x-ray tube |
US6289079B1 (en) | 1999-03-23 | 2001-09-11 | Medtronic Ave, Inc. | X-ray device and deposition process for manufacture |
US6319188B1 (en) * | 1999-04-26 | 2001-11-20 | Xoft Microtube, Inc. | Vascular X-ray probe |
US6195411B1 (en) | 1999-05-13 | 2001-02-27 | Photoelectron Corporation | Miniature x-ray source with flexible probe |
DE19925456B4 (en) * | 1999-06-02 | 2004-11-04 | Siemens Ag | X-ray tube and catheter with such an X-ray tube |
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US6464625B2 (en) | 1999-06-23 | 2002-10-15 | Robert A. Ganz | Therapeutic method and apparatus for debilitating or killing microorganisms within the body |
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 |
US6421416B1 (en) * | 2000-02-11 | 2002-07-16 | Photoelectron Corporation | Apparatus for local radiation therapy |
US6285735B1 (en) | 2000-02-11 | 2001-09-04 | Photoelectron Corporation | Apparatus for local radiation therapy |
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US6320935B1 (en) | 2000-02-28 | 2001-11-20 | X-Technologies, Ltd. | Dosimeter for a miniature energy transducer for emitting X-ray radiation |
ATE313355T1 (en) * | 2000-10-24 | 2006-01-15 | Radi Medical Technologies Ab | CATHETER SYSTEM WITH X-RAY TUBE |
US6551278B1 (en) * | 2000-11-10 | 2003-04-22 | Scimed Life Systems, Inc. | Miniature x-ray catheter with retractable needles or suction means for positioning at a desired site |
US6546080B1 (en) * | 2000-11-10 | 2003-04-08 | Scimed Life Systems, Inc. | Heat sink for miniature x-ray unit |
US6540720B1 (en) | 2000-11-10 | 2003-04-01 | Scimed Life Systems, Inc. | Miniature x-ray unit |
US6540655B1 (en) | 2000-11-10 | 2003-04-01 | Scimed Life Systems, Inc. | Miniature x-ray unit |
US6554757B1 (en) | 2000-11-10 | 2003-04-29 | Scimed Life Systems, Inc. | Multi-source x-ray catheter |
US20020110220A1 (en) * | 2000-11-22 | 2002-08-15 | Zilan Shen | Method and apparatus for delivering localized X-ray radiation to the interior of a body |
EP1217642A1 (en) * | 2000-12-22 | 2002-06-26 | Radi Medical Technologies AB | Active cooling of a miniature x-ray tube |
US6537195B2 (en) | 2001-05-07 | 2003-03-25 | Xoft, Microtube, Inc. | Combination x-ray radiation and drug delivery devices and methods for inhibiting hyperplasia |
US7041046B2 (en) * | 2001-05-07 | 2006-05-09 | Xoft, Inc. | Combination ionizing radiation and immunomodulator delivery devices and methods for inhibiting hyperplasia |
US6493419B1 (en) | 2001-06-19 | 2002-12-10 | Photoelectron Corporation | Optically driven therapeutic radiation source having a spiral-shaped thermionic cathode |
US6480568B1 (en) | 2001-06-19 | 2002-11-12 | Photoelectron Corporation | Optically driven therapeutic radiation source |
US6658086B2 (en) | 2001-06-19 | 2003-12-02 | Carl Zeiss | Optically driven therapeutic radiation source with voltage gradient control |
US20020191746A1 (en) * | 2001-06-19 | 2002-12-19 | Mark Dinsmore | X-ray source for materials analysis systems |
US6661876B2 (en) * | 2001-07-30 | 2003-12-09 | Moxtek, Inc. | Mobile miniature X-ray source |
US6721392B1 (en) | 2001-12-04 | 2004-04-13 | Carl-Zeiss-Stiftung | Optically driven therapeutic radiation source including a non-planar target configuration |
US6920202B1 (en) | 2001-12-04 | 2005-07-19 | Carl-Zeiss-Stiftung | Therapeutic radiation source with in situ radiation detecting system |
US6480573B1 (en) | 2001-12-04 | 2002-11-12 | Photoelectron Corporation | Therapeutic radiation source with increased cathode efficiency |
US6985557B2 (en) * | 2002-03-20 | 2006-01-10 | Minnesota Medical Physics Llc | X-ray apparatus with field emission current stabilization and method of providing x-ray radiation therapy |
US6661875B2 (en) | 2002-05-09 | 2003-12-09 | Spire Corporation | Catheter tip x-ray source |
US6925150B2 (en) | 2002-07-03 | 2005-08-02 | Cabot Microelectronics Corporation | Method and apparatus for providing a miniature, flexible voltage upconverter |
JP2005539351A (en) * | 2002-09-13 | 2005-12-22 | モックステック・インコーポレーテッド | Radiation window and manufacturing method thereof |
US7158612B2 (en) * | 2003-02-21 | 2007-01-02 | Xoft, Inc. | Anode assembly for an x-ray tube |
US6989486B2 (en) * | 2003-03-26 | 2006-01-24 | Xoft Microtube, Inc. | High voltage cable for a miniature x-ray tube |
US6987835B2 (en) * | 2003-03-26 | 2006-01-17 | Xoft Microtube, Inc. | Miniature x-ray tube with micro cathode |
KR20060002871A (en) * | 2003-03-26 | 2006-01-09 | 엑스오프트 마이크로튜브 인코포레이티드 | Miniature x-ray tube with micro cathode |
US20040218721A1 (en) * | 2003-04-30 | 2004-11-04 | Chornenky Victor I. | Miniature x-ray apparatus |
US7127033B2 (en) * | 2004-02-28 | 2006-10-24 | Xoft, Inc. | Miniature x-ray tube cooling system |
US7200203B2 (en) * | 2004-04-06 | 2007-04-03 | Duke University | Devices and methods for targeting interior cancers with ionizing radiation |
US7726318B2 (en) * | 2005-03-21 | 2010-06-01 | Xoft, Inc. | Radiation blocking patch for radio-therapy |
US7428298B2 (en) * | 2005-03-31 | 2008-09-23 | Moxtek, Inc. | Magnetic head for X-ray source |
US7382862B2 (en) * | 2005-09-30 | 2008-06-03 | Moxtek, Inc. | X-ray tube cathode with reduced unintended electrical field emission |
US20070250051A1 (en) * | 2006-04-25 | 2007-10-25 | Gaston Kerry R | Heating via microwave and millimeter-wave transmission using a hypodermic needle |
US7686755B2 (en) * | 2006-06-19 | 2010-03-30 | Xoft, Inc. | Radiation therapy apparatus with selective shielding capability |
US7737424B2 (en) * | 2007-06-01 | 2010-06-15 | Moxtek, Inc. | X-ray window with grid structure |
EP2006880A1 (en) * | 2007-06-19 | 2008-12-24 | Nederlandse Organisatie voor toegepast- natuurwetenschappelijk onderzoek TNO | Miniature X-ray source with guiding means for electrons and / or ions |
US7529345B2 (en) * | 2007-07-18 | 2009-05-05 | Moxtek, Inc. | Cathode header optic for x-ray tube |
US7756251B2 (en) * | 2007-09-28 | 2010-07-13 | Brigham Young Univers ity | X-ray radiation window with carbon nanotube frame |
US8498381B2 (en) | 2010-10-07 | 2013-07-30 | Moxtek, Inc. | Polymer layer on X-ray window |
US9305735B2 (en) | 2007-09-28 | 2016-04-05 | Brigham Young University | Reinforced polymer x-ray window |
EP2190778A4 (en) | 2007-09-28 | 2014-08-13 | Univ Brigham Young | Carbon nanotube assembly |
US8058612B2 (en) * | 2009-01-30 | 2011-11-15 | Georgia Tech Research Corporation | Microirradiators and methods of making and using same |
US8247971B1 (en) | 2009-03-19 | 2012-08-21 | Moxtek, Inc. | Resistively heated small planar filament |
US7983394B2 (en) | 2009-12-17 | 2011-07-19 | Moxtek, Inc. | Multiple wavelength X-ray source |
KR101068680B1 (en) * | 2010-02-03 | 2011-09-29 | 한국과학기술원 | Ultra-small X-ray tube using nanomaterial field emission source |
US8995621B2 (en) | 2010-09-24 | 2015-03-31 | Moxtek, Inc. | Compact X-ray source |
US8526574B2 (en) | 2010-09-24 | 2013-09-03 | Moxtek, Inc. | Capacitor AC power coupling across high DC voltage differential |
NL2005900C2 (en) * | 2010-12-22 | 2012-06-25 | Nucletron Bv | A mobile x-ray unit. |
US8804910B1 (en) | 2011-01-24 | 2014-08-12 | Moxtek, Inc. | Reduced power consumption X-ray source |
US8915833B1 (en) | 2011-02-15 | 2014-12-23 | Velayudhan Sahadevan | Image guided intraoperative simultaneous several ports microbeam radiation therapy with microfocus X-ray tubes |
US9636525B1 (en) | 2011-02-15 | 2017-05-02 | Velayudhan Sahadevan | Method of image guided intraoperative simultaneous several ports microbeam radiation therapy with microfocus X-ray tubes |
US8750458B1 (en) | 2011-02-17 | 2014-06-10 | Moxtek, Inc. | Cold electron number amplifier |
US8929515B2 (en) | 2011-02-23 | 2015-01-06 | Moxtek, Inc. | Multiple-size support for X-ray window |
US8792619B2 (en) | 2011-03-30 | 2014-07-29 | Moxtek, Inc. | X-ray tube with semiconductor coating |
US9076628B2 (en) | 2011-05-16 | 2015-07-07 | Brigham Young University | Variable radius taper x-ray window support structure |
US8989354B2 (en) | 2011-05-16 | 2015-03-24 | Brigham Young University | Carbon composite support structure |
US9174412B2 (en) | 2011-05-16 | 2015-11-03 | Brigham Young University | High strength carbon fiber composite wafers for microfabrication |
US8817950B2 (en) | 2011-12-22 | 2014-08-26 | Moxtek, Inc. | X-ray tube to power supply connector |
US8761344B2 (en) | 2011-12-29 | 2014-06-24 | Moxtek, Inc. | Small x-ray tube with electron beam control optics |
RU2519772C2 (en) * | 2012-03-27 | 2014-06-20 | Федеральное государственное унитарное предприятие "Научно-исследовательский институт Научно-производственное объединение "ЛУЧ" (ФГУП "НИИ НПО "ЛУЧ") | Method for exposing human body pathologies to radiation and device for implementing same (versions) |
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US9184020B2 (en) | 2013-03-04 | 2015-11-10 | Moxtek, Inc. | Tiltable or deflectable anode x-ray tube |
US9177755B2 (en) | 2013-03-04 | 2015-11-03 | Moxtek, Inc. | Multi-target X-ray tube with stationary electron beam position |
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US9173623B2 (en) | 2013-04-19 | 2015-11-03 | Samuel Soonho Lee | X-ray tube and receiver inside mouth |
JP6327802B2 (en) * | 2013-06-12 | 2018-05-23 | キヤノン株式会社 | Radiation generating tube, radiation generating apparatus and radiation imaging system using the same |
US11101096B2 (en) * | 2014-12-31 | 2021-08-24 | Rad Source Technologies, Inc. | High dose output, through transmission and relective target X-ray system and methods of use |
US9818569B2 (en) * | 2014-12-31 | 2017-11-14 | Rad Source Technologies, Inc | High dose output, through transmission target X-ray system and methods of use |
US10086213B2 (en) | 2015-04-23 | 2018-10-02 | Mark A. D'Andrea | Mobile gynecological balloon devices and methods |
RU179629U1 (en) * | 2018-01-16 | 2018-05-21 | Федеральное государственное унитарное предприятие "Научно-исследовательский институт Научно-производственное объединение "ЛУЧ" (ФГУП "НИИ НПО "ЛУЧ") | MINIATURE SOURCE OF X-RAY RADIATION |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1881448A (en) * | 1928-08-15 | 1932-10-11 | Formell Corp Ltd | X-ray method and means |
US3714486A (en) * | 1970-10-07 | 1973-01-30 | Crary J Mc | Field emission x-ray tube |
US4701941A (en) * | 1983-02-08 | 1987-10-20 | Commonwealth Scientific And Industrial Research Organization (Csiro) | Radiation source |
Family Cites Families (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4702228A (en) * | 1985-01-24 | 1987-10-27 | Theragenics Corporation | X-ray-emitting interstitial implants |
-
1990
- 1990-11-21 US US07/616,397 patent/US5090043A/en not_active Ceased
-
1991
- 1991-10-25 WO PCT/US1991/007907 patent/WO1992009998A1/en not_active Application Discontinuation
- 1991-10-25 JP JP4500815A patent/JPH06502559A/en active Pending
- 1991-10-25 EP EP92902061A patent/EP0560906A1/en not_active Ceased
-
1992
- 1992-04-17 US US07/870,145 patent/USRE34421E/en not_active Expired - Lifetime
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1881448A (en) * | 1928-08-15 | 1932-10-11 | Formell Corp Ltd | X-ray method and means |
US3714486A (en) * | 1970-10-07 | 1973-01-30 | Crary J Mc | Field emission x-ray tube |
US4701941A (en) * | 1983-02-08 | 1987-10-20 | Commonwealth Scientific And Industrial Research Organization (Csiro) | Radiation source |
Non-Patent Citations (1)
Title |
---|
Dunlee Stationary Anode Inserts DL-1 to DL-7, Dunlee Corporation Bellwood, Illinois, issued June 1972. * |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0630039A1 (en) * | 1993-06-18 | 1994-12-21 | Hamamatsu Photonics K.K. | X-ray generation tube |
EP0630038A1 (en) * | 1993-06-18 | 1994-12-21 | Hamamatsu Photonics K.K. | X-ray generation tube |
US5504799A (en) * | 1993-06-18 | 1996-04-02 | Hamamatsu Photonics K.K. | X-ray generation tube for ionizing ambient atmosphere |
US5504798A (en) * | 1993-06-18 | 1996-04-02 | Hamamatsu Photonics K. K. | X-ray generation tube for ionizing ambient atmosphere |
Also Published As
Publication number | Publication date |
---|---|
JPH06502559A (en) | 1994-03-24 |
EP0560906A4 (en) | 1994-04-20 |
USRE34421E (en) | 1993-10-26 |
EP0560906A1 (en) | 1993-09-22 |
US5090043A (en) | 1992-02-18 |
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