Connect public, paid and private patent data with Google Patents Public Datasets

Miniature radiation source with flexible probe and laser driven thermionic emitter

Download PDF

Info

Publication number
US20010016027A1
US20010016027A1 US09748590 US74859000A US2001016027A1 US 20010016027 A1 US20010016027 A1 US 20010016027A1 US 09748590 US09748590 US 09748590 US 74859000 A US74859000 A US 74859000A US 2001016027 A1 US2001016027 A1 US 2001016027A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
source
radiation
electron
target
probe
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.)
Granted
Application number
US09748590
Other versions
US6320932B2 (en )
Inventor
Mark Dinsmore
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.)
Carl Zeiss AG
Original Assignee
Mark Dinsmore
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

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/10X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1001X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
    • HELECTRICITY
    • H01BASIC ELECTRIC ELEMENTS
    • H01JELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00X-ray tubes
    • H01J35/02Details
    • H01J35/04Electrodes mutual position thereof and constructional adaptations of the electrodes therefor
    • H01J35/06Cathodes
    • H01J35/065Field emission, photo emission or secondary emission cathodes
    • HELECTRICITY
    • H01BASIC ELECTRIC ELEMENTS
    • H01JELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00X-ray tubes
    • H01J35/32Tubes 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
    • HELECTRICITY
    • H01BASIC ELECTRIC ELEMENTS
    • H01JELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00X-ray tubes
    • H01J2235/08Targets (anodes) and X-ray converters
    • H01J2235/086Target geometry
    • H01J2235/087Transmission type
    • HELECTRICITY
    • H01BASIC ELECTRIC ELEMENTS
    • H01JELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00X-ray tubes
    • H01J2235/16Vessels
    • H01J2235/163Vessels shaped for a particular application
    • H01J2235/164Small cross-section, e.g. for entering in a body cavity

Abstract

This invention is directed to a radiation source comprising a power supply, a flexible fiber optic cable assembly, a light source, and a target assembly. The power supply includes a first terminal and a second terminal, and elements for establishing an output voltage between the first terminal and the second terminal. The flexible fiber optical cable assembly has an originating end and a terminating end, and includes a fiber optical element extending from the originating end to the terminating end. The cable is adapted for transmitting light incident on the originating end to the terminating end. The light source includes elements for generating a beam of light at and directed to the originating end of the fiber optical cable assembly. The target assembly is affixed to the terminating end of the fiber optical cable assembly and is electrically coupled to the power supply by way of the first terminal and the second terminal. The target assembly includes elements for emitting radiation in a predetermined spectral range, in response to light transmitted to the terminating end.

Description

    BACKGROUND OF THE INVENTION
  • [0001]
    The present invention relates to a highly miniaturized, low power, programmable radiation source for use in delivering predefined doses of radiation to a predefined region and more particularly to a miniaturized radiation source mounted in a flexible probe.
  • [0002]
    In the field of medicine, radiation is used for diagnostic, therapeutic and palliative treatment of patients. The conventional medical radiation sources used for these treatments include large fixed position machines as well as small, transportable radiation generating probes. The current state of the art treatment systems utilize computers to generate complex treatment plans.
  • [0003]
    These systems apply doses of radiation that are known to inhibit the growth of new tissue because the radiation affects dividing cells more than the mature cells found in non-growing tissue. Thus, the tissue in the site of an excised tumor can be treated to prevent the regrowth of cancerous tissue and the recurrence of cancer. Alternatively, radiation can be applied to other areas of the body to inhibit tissue growth, for example the growth of new blood vessels inside the eye that can cause macular degeneration.
  • [0004]
    Conventional radiation treatments systems, such as the LINAC used for medical treatment, utilize a high power remote radiation source and direct a beam of radiation at a target area, such as tumor inside the body of a patient. This type of treatment is referred to as teletherapy because the radiation source is located a predefined distance, approximately one meter, from the target. This treatment suffers from the disadvantage that tissue disposed between the radiation source and the target is exposed to radiation.
  • [0005]
    An alternative treatment system utilizing a point source of radiation is disclosed in U.S. Pat. No. 5,153,900 issued to Nomikos et al., U.S. Pat. No. 5,369,679 to Sliski et al., and U.S. Pat. No. 5,422,926 to Smith et al., all owned by the assignee of the present application, all of which are hereby incorporated by reference. This system includes a miniaturized, insertable probe capable of producing low power radiation in predefined dose geometries disposed about a predetermined location. This type of treatment is referred to as brachytherapy because the source is located close to or in some cases within the area receiving treatment. One advantage of brachytherapy is that the radiation is applied primarily to treat a predefined tissue volume, without significantly affecting the tissue adjacent to the treated volume.
  • [0006]
    Typical radiation therapy treatment involves positioning the insertable probe into or adjacent to the tumor or the site where the tumor or a portion of the tumor was removed to treat the tissue adjacent the site with a “local boost” of radiation. In order to facilitate controlled treatment of the site, it is desirable to support the tissue portions to be treated at a predefined distances from the radiation source. Alternatively, where the treatment involves the treatment of surface tissue or the surface of an organ, it is desirable to control the shape of the surface as well as the shape of the radiation field applied to the surface.
  • [0007]
    The treatment can involve the application of radiation, either continuously or intermittently, over an extended period of time. Therefore, it is desirable that the insertable probe be adjustably supported in a compliant manner to accurately position the radiation source with respect to the treated site and accommodate normal minor movements of the patient, such as movements associated with breathing.
  • [0008]
    In many x-ray therapeutic procedures, x-ray probes of the type generally disclosed in U.S. Pat. No. 5,153,900 incorporate a relatively rigid tube enclosing an electron beam directed to an x-ray emitting target at its distal end. For example, in treatment of brain tumors, an x-ray probe having a rigid tube is used with a stereotactic frame affixed to the patient's skull, where the tube is advanced into a biopsy hole to the tumor location, as disclosed in U.S. Pat. No. 5,369,679. The rigidity of the tube is useful in ensuring that the x-ray emitting target is properly located. In other cases, it is desirable to have a flexible tube leading to the x-ray emitting target, for example, where it is desirable to pass the probe up the urethra to the bladder, for treatment of the bladder. Such a flexible probe is disclosed in U.S. Pat. No. 5,248,658.
  • [0009]
    However, it has been difficult to effectively treat tissue using the flexible probe of the latter patent.
  • [0010]
    Accordingly, it is an object of the present invention to provide an improved system for delivering radiation to a localized area.
  • [0011]
    It is a further object of the present invention to provide an improved highly miniaturized radiation source with a flexible probe.
  • SUMMARY OF THE INVENTION
  • [0012]
    The present invention is directed to a miniaturized radiation source at the end of a flexible probe or catheter. The flexible catheter extends along a probe axis between a proximal end and a distal end of the catheter. The radiation source, at the distal end of the catheter, includes a substantially rigid housing disposed about a substantially evacuated interior region extending along a beam axis from an electron source at an input end of the housing to a radiation transmissive window at an output end of the housing. The housing also includes a channel electron multiplier adapted for receiving electrons from the electron source and for producing free electrons at an output end of the channel electron multiplier and an electron accelerator adapted for establishing a potential difference in the interior region of the housing whereby the free electrons produced at the output end of the channel electron multiplier are accelerated toward a target at or near the window. The target produces x-radiation in response to incident accelerated free electrons.
  • [0013]
    Preferably, the electron accelerator includes a surface disposed about the beam axis between the electron source and the target on a ceramic and preferably monolithic, substrate. In one embodiment, the surface bears a semiconductor coating. The surface may be substantially conical in shape wherein the distance from the beam axis increases as a function of the distance from the electron source. The electron source can be a photocathode illuminated by laser energy, a field emitter or a thermionic emitter. The target and outer surface of the probe is preferably maintained at ground potential to reduce the risk of shock.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • [0014]
    The foregoing and other objects of this invention, the various features thereof, as well as the invention itself, may be more fully understood from the following description, when read together with the accompanying drawings in which:
  • [0015]
    [0015]FIGS. 1A and 1B are a diagrammatic perspective view and a diagrammatic detail view, respectively, of a low power radiation source embodying the present invention;
  • [0016]
    [0016]FIGS. 2A and 2B are a perspective view and a sectional view, respectively, of an alternate form embodying the present invention;
  • [0017]
    [0017]FIG. 3 is a diagrammatic representation of a sheath adapted for use with the apparatus of FIG. 1;
  • [0018]
    [0018]FIG. 4 is a schematic block diagram of the embodiment of FIG. 1;
  • [0019]
    [0019]FIG. 5 is a diagrammatic view of a low power radiation treatment system having a flexible probe embodying the present invention; and
  • [0020]
    [0020]FIG. 6 is a diagrammatic view of a low power radiation source embodying the present invention.
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • [0021]
    The present invention is directed to a miniature, low power radiation producing probe which can be used for diagnostic, therapeutic and palliative treatment of patients. The radiation source in accordance with the present invention can made smaller than conventional radiation sources. In addition, the radiation source can be disposed at the distal end of the tip of a flexible (or rigid) tube or catheter which can be inserted into the body. In one embodiment, only a single high voltage wire is necessary for operation. The target and the outer surface of the probe are set at the ground potential to reduce the shock hazard of the device.
  • [0022]
    [0022]FIG. 1A shows an x-ray apparatus 10 embodying the present invention. Apparatus 10 includes a housing 12 and an elongated cylindrical probe 14 extending from housing 12 along a reference axis 16 to an x-ray source assembly 19. Preferably, the probe 14 is flexible, as described below, but in some cases may be rigid. The housing 12 encloses a high voltage power supply 12A, a battery 12B and a control system 12C. The x-ray source assembly 19 has an electron source (cathode) 22 located in the distal end of the probe 14. Electron source 22 is located in close proximity to a channel electron multiplier (CEM) 23 which receives electrons from the electron source 22. An accelerator 24 is positioned between the CEM 23 and an x-ray emitting (in response to incident accelerated electrons) target 26. The target underlies on x-ray transmissive window 27. Probe 14 is integral with the housing 12 and extends toward the target 26. In various embodiments, the x-ray emitting tip may be selectively shielded to control the spatial distribution of x-rays. In addition, the accelerator 24 may be magnetically shielded to prevent external magnetic fields from deflecting the beam away from designed impact points on the target.
  • [0023]
    [0023]FIG. 1B shows an x-ray source assembly 19′ for generating x-rays embodying the present invention. That source 19′ is adapted for placement at the end of a cylindrical element (flexible or rigid). In an alternate form, shown in FIG. 2A and 2B, an x-ray source 19″ is positioned within a compact housing 12, the latter device is suitable to applying x-radiation body surface tissue.
  • [0024]
    In the various forms of x-ray source assembly 19, the electron beam generator 22 may include a thermionic emitter (driven by a low voltage power source or laser) or a photocathode (irradiated by an LED or laser source) or a field emitter. A single high voltage power supply 12A can be used to power the electron source (thermionic emitter) 22, the CEM 23 and accelerator 24. The accelerator 24 establishes an acceleration potential difference between the CEM 23 and the target 26 which is at ground potential. The beam generation and acceleration components can be adapted to establish a thin (e.g. 1 mm or less in diameter) electron beam within the assembly 19 along a nominally straight axis 16.
  • [0025]
    Preferably, the CEM 23 is constructed as is well known and the electron multiplication value is predetermined as function of the intended use of the radiation source. Preferably, a high voltage of 1 K volt is connected to input end of the CEM.
  • [0026]
    Preferably, the accelerator is constructed from a monolithic ceramic material and includes an interior channel formed in the shape of the surface of a cone, although other shapes may be used, for example parabolic. The accelerator is disposed between the CEM 23 and the target 26 along the axis of the electron beam trajectory whereby the distance of the surface from the beam increases as a function of the distance from the CEM 23. Preferably, the surface includes a semiconductive coating 24A which ensures that the voltage gradient in the accelerator is smooth and linear and helps to prevent breakdown which occurs when the electrons hit the walls of the accelerator.
  • [0027]
    In one form of the invention, the outer cylindrical portion of the x-ray source assembly 19 is a hollow evacuated cylinder made of a molybdenum-rhenium, (Mo-Re), molybdenum (Mo) or mu-metal body with an interior diameter of 2 mm, and an exterior diameter of 3 mm. Preferably, beryllium (Be) cap and having a distance from the electron source to the target is less than 2 mm. The target assembly 26 includes an emission element consisting of a small beryllium (Be) target element 26A which is coated on the side exposed to the incident electron beam with a thin film or layer 26B of a high-Z element, such as tungsten (W), uranium (U) or gold (Au). By way of example, with electrons accelerated to 30 keV-, a 2.2 micron thick tungsten film absorbs substantially all the incident electrons, while transmitting approximately 95% of any 30 keV-, 88% of any 20 keV-, and 83% of any 10 keV- x-rays generated in that layer. In the preferred embodiment, the beryllium target element 26A is 0.5 mm thick with the result that 95% of the x-rays generated in directions normal to and toward the substrate 26A, and having passed through the tungsten target, are then transmitted through the beryllium substrate and outward at the distal end of assembly 19. While the target element 26A shown in FIG. 3B is in the form of a hemispherical layer, other shaped elements may be used, such as those having disk-like or conical shapes.
  • [0028]
    In some forms of the target, the window element 26A may include a multiple layer film 26B, where the differing layers may have different emission characteristics. By way of example, the first layer may have an emission (vs. energy) peak at a relatively low energy, and the second (underlying) layer may have an emission (vs. energy) peak at a relatively high energy. With this form of the invention, a low energy electron beam may be used to generate x-rays in the first layer (to achieve a first radiation characteristic) and high energy electrons may be used to penetrate through to the underlying layer (to achieve a second radiation characteristic). As an example, a 0.5 mm wide electron beam is emitted at the cathode and accelerated to 30 keV- through the anode, with 0.1 eV transverse electron energies, and arrives at the target assembly 26 downstream from the anode, with a beam diameter of less than 1 mm at the target assembly 26. X-rays are generated in the target assembly 26 in accordance with preselected beam voltage, current, and target element 26B composition. The x-rays thus generated pass through the beryllium target substrate 26A with minimized loss in energy. As an alternative to beryllium, the target substrate 26A may be made of carbon or other suitable material which permits x-rays to pass with a minimum loss of energy. An optimal material for target substrate 26A is carbon in its diamond form, since that material is an excellent heat conductor. Using these parameters, the resultant x-rays have sufficient energy to penetrate into soft tissues to a depth of a centimeter or more, the exact depth dependent upon the x-ray energy distribution.
  • [0029]
    The apparatus of FIGS. 2A and 2B is particularly adapted for full implantation into a patient, where the housing 12 a biocompatible outer surface and encloses both a high voltage power supply circuit 12A for establishing a drive voltage for the beam generator 22, and an associated battery 12B for driving that circuit 12A. In this case, an associated controller 12C establishes control of the output voltage of the high power supply circuit 12A, in the manner described below.
  • [0030]
    The apparatus of FIGS. 1A and 1B may be used in a manner where only the probe 14 and x-ray source assembly 19 are inserted into a patient while the housing 12 remains outside the patient, i.e., a transcutaneous form. In the latter form, some or all of the various elements shown within housing 12 may alternatively be remotely located.
  • [0031]
    In the transcutaneous form, the apparatus 10 may be used with an elongated closed end (or cup-shaped) sheath 34, as shown in FIG. 3, having a biocompatible outer surface, for example, fabricated of medical grade aliphatic polyurethane, as manufactured under the trademark Tecoflex by Thermedics, Inc., Woburn, Mass. With this configuration, the probe 14 is first inserted into the sheath 34. The sheath 34 and probe 14 are then inserted into the patient through the skin. Alternatively, a port may be inserted through the skin and attached to it, as for example a Dermaport port manufactured by Thermedics Inc., Woburn, Mass. The probe 14 is then inserted into the port.
  • [0032]
    The lining of the sheath or port can be configured as an x-ray shield by introducing barium sulfate or bismuth trioxide, or other x-ray shielding materials, into the sheath. If necessary, the probe 14 and housing 12 can be secured to the patient's body to prevent any relative motion during the extended time of treatment. An exemplary sheath 34 is shown in FIG. 3.
  • [0033]
    In one embodiment of the apparatus as shown in FIGS. 1A and 1B, the main body of the probe 14 can be made of a magnetically shielding material such as a mu-metal. Alternatively, the probe 14 can be made of a non-magnetic metal, preferably having relatively high values for Young's modulus and elastic limit. Examples of such material include molybdenum, rhenium or alloys of these materials. The outer cylindrical shell of the accelerator 24 can be made of the outer shell metal. The inner or outer surface of probe 14 can then be coated with a high permeability magnetic alloy such as permalloy (approximately 80% nickel and 20% iron), to provide magnetic shielding. Alternatively, a thin sleeve of mu-metal can be fitted over, or inside of that shell of accelerator 24. The x-ray apparatus 10 can then be used in environments in which there are dc and ac magnetic fields due to electrical power, the field of the earth, or other magnetized bodies nominally capable of deflecting the electron beam from the probe axis.
  • [0034]
    In implantable configurations, such as those of FIGS. 2A and 2B, the power supply 12A and target assembly 26 are preferably enclosed in a capsule to prevent current flow from the x-ray source to the patient. The closed housing 12 and probe 14 are, thus, encapsulated in a continuous outer shell of appropriate shielding material such as those mentioned previously.
  • [0035]
    The high voltage power supply 12A in each of the illustrated embodiments preferably satisfies three criteria: 1) small in size; 2) high efficiency to enable the use of battery power; and 3) independently variable x-ray tube voltage and current to enable the unit to be programmed for specific applications. A high-frequency, switch-mode power converter is used to meet these requirements. The most appropriate topology for generating low power and high voltage is a resonant voltage converter working in conjunction with a high voltage, Cockroft-Walton-type multiplier. Low-power dissipation, switch-mode power-supply controller-integrated circuits (IC) are currently available for controlling such topologies with few ancillary components.
  • [0036]
    The embodiment of FIGS. 2A and 2B can also be adapted for superficial usage, that is for direct placement on the skin of a patient. This form of the invention is particularly useful for x-ray treatment of skin lesions or tumors, or other dermatological applications. In FIGS. 2A and 2B, elements that correspond to elements in the embodiment of FIGS. 1A and 1B are denoted with the same reference designations. Apparatus 10′ generates an electron beam in a channel 40 enclosed within housing 12, where that channel 40 corresponds to probe 14. In the present embodiment, of FIGS. 2A and 2B, the x-ray source assembly 19 functions in a manner similar to that described above. With the configuration of FIGS. 2A and 2B, low power x-rays may be directed to a desired skin region of a patient.
  • [0037]
    In all of the above-described embodiments, the x-ray emission element of the target assembly is adapted to be adjacent to or within the region to be irradiated. The proximity of the emission element to the targeted region, e.g. the tumor, eliminates the need for the high voltages of presently used machines, to achieve satisfactory x-ray penetration through the body wall to the tumor site. The low voltage also concentrates the radiation in the targeted tumor, and limits the damage to surrounding tissue and surface skin at the point of penetration. For example, the delivery of 4000 rads, as is required after a mastectomy, with a 40 kV, 20 uA electron beam, may require approximately 1 to 3 hours of radiation. However, since the x-ray source is, in this preferred embodiment, insertable proximate to, or into, the region-to-be-irradiated risk of incidental radiation exposure to other parts of the patient's body is significantly reduced.
  • [0038]
    Further, specificity in treating tumors may be achieved by tailoring the target and shield geometry and material at the emission site, for example as disclosed in U.S. Pat. No. PHLL-111, assigned to the assignee of the present invention. This tailoring facilitates the control of energy and the spatial profile of the x-ray emission to ensure more homogenous distribution of the radiation throughout the targeted tumor.
  • [0039]
    [0039]FIG. 4 is a schematic representation of the x-ray source apparatus 10 shown in FIG. 1A. In that preferred configuration, the housing 12 is divided into a first portion 12′ and a second portion 12″. Enclosed within the first housing portion 12′ is a rechargeable battery 12B, a recharge network 12D for the battery 12B, which is adapted for use with an external charger 50, and a telemetry network 12E, adapted to be responsive to an external telemetry device 52 to function in the manner described below. That portion 12′ is coupled by cables to the second housing portion 12″. The second housing portion 12″ includes the high voltage power supply 12A, controller 12C and the probe 14, as well as the electron beam generating element 22. In one embodiment, the electron beam generator includes a thermionic emitter 22 driven by the power supply 12A. In operation, power supply 12A heats the thermionic emitter 22, which in turn generates electrons which are then accelerated toward the anode 24. The anode 24 attracts the electrons, but passes them through its central aperture toward the target assembly 26. The controller 12C controls the power supply 12A to dynamically adjust the cathode voltage, the electron beam current, and temporal parameters, or to provide pre-selected voltage, beam current, and temporal parameters.
  • [0040]
    Also illustrated, is an alternative electron beam generator which includes a photoemitter 22 irradiated by a light source 56, such as a diode laser or LED, powered by a driver 55. The light is focused on the photoemitter 22 by a focusing lens 58.
  • [0041]
    In the illustrated embodiment, external telemetry device 52 and telemetry network 12E cooperate to permit external control (dynamic or predetermined) control over the power supply 12A and temporal parameters. In embodiments when the housing 12″ is not implanted, but where only probe 14 extends into a patient's body, the controller 12C may directly be used to control operation and in that case there is no need for network 12E.
  • [0042]
    [0042]FIGS. 5 and 6 show a diagrammatic view of radiation treatment apparatus 200 including a flexible probe 214. The apparatus 200 includes a high voltage source 218, a laser (or other optical) source 220, a probe assembly 214, and a radiation source assembly 226. According to one aspect of the invention, the apparatus 200 provides the required flexibility, without using strong magnetic fields, by locating electron source components 222, 223 and accelerator 224 near the target 228 in the distal end of the probe 214. The probe assembly 214 couples both the laser source 220 and the high voltage feed 218 to the radiation source assembly 226. Preferably, the probe assembly includes flexible fiber optical cable 202 enclosed in a small-diameter flexible metallic tube 204.
  • [0043]
    The radiation source assembly 226, which can be for example 1 to 2 cm in length, extends from the end of the probe assembly 214 and includes a shell which encloses the target 228. According to one embodiment, the radiation source assembly 226 is rigid in nature and generally cylindrical in shape. In this embodiment the cylindrical shell enclosing the radiations source assembly 226 can be considered to provide a housing for the electron beam source as well as a tubular probe extending from the housing along the electron beam path. The inner surface 226A of the assembly 226 is lined with an electrical insulator, while the external surface of the assembly 226 is electrically conductive. According to a preferred embodiment, the radiation source assembly is hermetically sealed to the end of the probe assembly 214, and evacuated. According to another embodiment, the entire probe assembly 214 is evacuated.
  • [0044]
    The terminal end 202A of the fiber optical cable 202 is preferably coated, over at least part of its area, with a semitransparent photoemissive substance such as, Ag-O-Cs, thus forming a photocathode 222. A high voltage conductor 208, embedded in the fiber optical cable 202, conducts electrons to the cathode 222 (if necessary), the electron multiplier 223 and the accelerator 224 from the high voltage source 218. Similarly, the flexible tube 204 couples a ground return from the target 228 to the high voltage source 218, thereby establishing a high voltage field between the cathode 216 and the target 228. The fiber optical cable 202 acts as an insulating dielectric between the high voltage conductor 208 and the grounded flexible tube 204.
  • [0045]
    In order to eliminate scattering of the light in the fiber optic cable 202 by the high voltage wire 208, the fiber optic cable 202 can have an annular configuration. The light from the laser 220 travels down the annular core of the fiber optic cable 202. Cladding can be provided on each side of the core having an index of refraction so as to reflect the light beam incident on the interface back into the core. The grounded flexible metal tube 204 can surround the outer cladding.
  • [0046]
    As in previously described embodiments, the target 228 can be for example, beryllium, (Be), coated on one side with a thin film or layer 228A of a higher impedance element, such as tungsten (W) or gold (Au).
  • [0047]
    In operation, the small semiconductor laser 220 shining down the fiber optical cable 202 activates the transmissive photocathode 222 which generates free electrons 216. The high voltage field between the cathode 222 and target 228 accelerates these electrons, thereby forcing them to strike the surface 228A of target 228 and produce x-rays. In order to generate, for example, 20 uA of current from an Ag-O-Cs photocathode 222 with a laser 220 emitting light at a wavelength of 0.8 m, the 0.4% quantum efficiency of this photocathode 222 for this wavelength requires that the laser 220 emits 7.5 mW optical power. Such diode lasers are readily commercially available. According to the invention, the photoemissive surface which forms cathode 222 can, in fact, be quite small. For example, for a current density at the cathode 222 of 1 A/cm2, the photoemitter's diameter need only be approximately 50 μm.
  • [0048]
    One difficult fabrication aspect of this invention is the fabrication of the photocathode 222, which for practical substances, with reasonable quantum efficiencies above 10−3, should be performed in a vacuum. This procedure can be carried out with the fiber optical cable 202 positioned in a bell jar, where for example, an Ag-O-Cs photosurface is fabricated in the conventional manner. Subsequently, without exposure to air, the optical cable 202 can be inserted into the tube 204. The end 202B can be vacuum sealed to the flexible tube 204.
  • [0049]
    In the above embodiments, the probe 14 or 214, along with its associated target 26, or 228, can be coated with a biocompatible outer layer, such as titanium nitride on a sublayer of nickel. For additional biocompatibility, a sheath of, for example, polyurethane can be fitted over the probe, such as that illustrated in FIG. 3.
  • [0050]
    The invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. The present embodiments are therefore to be considered in respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of the equivalency of the claims are therefore intended to be embraced therein.

Claims (15)

What is claimed is:
1. A miniature radiation source comprising:
a flexible catheter extending along a probe axis between a proximal end and a distal end of the catheter;
a radiation source having a substantially rigid housing defining a substantially evacuated interior region extending along a beam axis between an electron source at an input end of the housing and a radiation transmissive window at an output end of the housing, the housing having a target responsive to incident accelerated free electrons to emit radiation whereby the radiation emitted therefrom is directed through the radiation transmissive window, the housing having the input end affixed to the distal end of the catheter;
means responsive to a signal at the proximal end of the catheter for selectively activating the electron source to emit free electrons in the interior region
a channel electron multiplier adapted for receiving electrons from the electron source, at an input end, and adapted for producing free electrons at an output end; and
an electron accelerator adapted for establishing a potential difference in the interior region of the radiation source whereby the free electrons are accelerated toward the target.
2. A miniature radiation source according to
claim 1
, wherein the electron accelerator includes a surface disposed about the beam axis between the electron source and the target and being characterized as having an increasing distance from the beam axis as a function of distance from the electron source, the surface bearing a semiconductor coating.
3. A miniature radiation source according to
claim 2
, wherein the surface is established by a monolithic ceramic element.
4. A miniature radiation source according to claims 2, wherein the surface is a surface of revolution.
5. A miniature radiation source according to claims 2, wherein the function is linear.
6. A miniature radiation source according to
claim 1
, wherein the electron source is selected from the group including a photocathode illuminated by laser energy, a field emitter, and a thermionic emitter.
7. A miniature radiation source according to
claim 1
, wherein the target is at ground potential.
8. A therapeutic radiation source adapted for coupling to a catheter, comprising:
a radiation source having a substantially rigid housing defining a substantially evacuated interior region extending along a beam axis between an electron source at an input end of the housing and a radiation transmissive window at an output end of the housing, the radiation source having a target responsive to incident accelerated free electrons to emit radiation disposed along the beam axis whereby the radiation emitted therefrom is directed through the radiation transmissive window, the electron source generating the electrons in response to a signal communicated through the catheter, the window being at ground potential; and
a ceramic monolithic accelerator for accelerating the electrons along the beam axis, the accelerator having a hollow interior for passing electrons therethrough, the interior diverging away from electron source, the interior being coated with a semiconductor coating to provide a smooth voltage gradient along the beam axis and to reduce secondary emissions from the accelerator.
9. A therapeutic radiation source according to
claim 8
, further comprising means connecting the coating to a control voltage in the catheter for modifying electron acceleration through the accelerator.
10. A therapeutic radiation source according to
claim 8
, further comprising a channel electron multiplier adjacent to the source for multiplying electrons for acceleration within the accelerator.
11. A therapeutic radiation source according to
claim 8
, wherein the interior comprises a single cylindrical wall.
12. A therapeutic radiation source according to
claim 8
, wherein the electron source is selected from the group consisting of a photocathode illuminated by laser energy, a field emitter, and a thermionic emitter.
13. A therapeutic radiation source according to
claim 8
, wherein the source comprises a channel electron multiplier.
14. A radiation source for attachment to a therapeutic probe, the radiation source having an elongated rigid housing defining a substantially evacuated interior region extending along a beam axis, said radiation source comprising:
an electron source for producing free electrons;
a ceramic monolithic accelerator for accelerating the free electrons toward a radiation target, the accelerator having a hollow interior for passing electrons therethrough, the interior diverging away from electrons of increasing acceleration, the interior being coated with a semiconductor coating to provide a substantially smooth voltage gradient between high voltage and ground potential and to reduce secondary emissions from the accelerator, the radiation target converting accelerated electrons into radiation;
an radiation window, coupled to ground potential, for passing the radiation through the housing.
15. A radiation source according to
claim 14
where in said electron source comprises an electron generator and an electron multiplier, said electron multiplier being adapted for producing a quantity of free electrons as a function of a quantity of electrons produced by said electron generator.
US09748590 1999-05-13 2000-12-22 Miniature radiation source with flexible probe and laser driven thermionic emitter Active US6320932B2 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US09311792 US6195411B1 (en) 1999-05-13 1999-05-13 Miniature x-ray source with flexible probe
US09748590 US6320932B2 (en) 1999-05-13 2000-12-22 Miniature radiation source with flexible probe and laser driven thermionic emitter

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US09748590 US6320932B2 (en) 1999-05-13 2000-12-22 Miniature radiation source with flexible probe and laser driven thermionic emitter

Publications (2)

Publication Number Publication Date
US20010016027A1 true true US20010016027A1 (en) 2001-08-23
US6320932B2 US6320932B2 (en) 2001-11-20

Family

ID=23208494

Family Applications (2)

Application Number Title Priority Date Filing Date
US09311792 Active US6195411B1 (en) 1999-05-13 1999-05-13 Miniature x-ray source with flexible probe
US09748590 Active US6320932B2 (en) 1999-05-13 2000-12-22 Miniature radiation source with flexible probe and laser driven thermionic emitter

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US09311792 Active US6195411B1 (en) 1999-05-13 1999-05-13 Miniature x-ray source with flexible probe

Country Status (3)

Country Link
US (2) US6195411B1 (en)
EP (1) EP1208582A4 (en)
WO (1) WO2000070645A8 (en)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020115902A1 (en) * 2001-02-22 2002-08-22 Dejuan Eugene Beta radiotherapy emitting surgical device and methods of use thereof
WO2002103743A1 (en) * 2001-06-19 2002-12-27 Photoelectron Corporation X-RAY SOURCE FOR MATERIALS ANALYSIS SYSTEMs
JP2006524881A (en) * 2003-01-16 2006-11-02 カールツァイスシュティフトゥング、ディー/ビー/エイ カールツァイス、オーバーコーへン、ジャーマニー Thermally regulated by a field emission cathode and beam current measurement techniques
US20060258895A1 (en) * 2005-05-12 2006-11-16 Siemens Aktiengesellschaft Catheter, catheter device and imaging diagnostic apparatus
US20070055089A1 (en) * 2004-02-12 2007-03-08 Larsen Charles E Methods and apparatus for intraocular brachytherapy
GB2446505A (en) * 2008-02-05 2008-08-13 Gen Electric X-ray generation using a secondary emission electron source
US20100094266A1 (en) * 2007-04-04 2010-04-15 The Regents Of The University Of California Laser activated micro accelerator platform
US7803103B2 (en) 2005-02-11 2010-09-28 Neovista Inc. Methods and apparatus for intraocular brachytherapy
US8353812B2 (en) 2008-06-04 2013-01-15 Neovista, Inc. Handheld radiation delivery system
WO2014152515A1 (en) * 2013-03-15 2014-09-25 Varian Medical Systems, Inc. Energy degrader for radiation therapy system

Families Citing this family (38)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6407492B1 (en) * 1997-01-02 2002-06-18 Advanced Electron Beams, Inc. Electron beam accelerator
US6450407B1 (en) 1998-04-17 2002-09-17 Viztec, Inc. Chip card rebate system
US6320935B1 (en) * 2000-02-28 2001-11-20 X-Technologies, Ltd. Dosimeter for a miniature energy transducer for emitting X-ray radiation
US6811562B1 (en) * 2000-07-31 2004-11-02 Epicor, Inc. Procedures for photodynamic cardiac ablation therapy and devices for those procedures
DE60213389D1 (en) 2001-03-20 2006-09-07 Advanced Electron Beams Inc X-ray irradiation device
US7133493B2 (en) * 2001-03-20 2006-11-07 Advanced Electron Beams, Inc. X-ray irradiation apparatus
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
JP4268037B2 (en) * 2001-06-19 2009-05-27 フォトエレクトロン コーポレイション Optical driven therapeutic radiation source
US6658086B2 (en) * 2001-06-19 2003-12-02 Carl Zeiss Optically driven therapeutic radiation source with voltage gradient control
US20030063707A1 (en) * 2001-10-01 2003-04-03 Mulhollan Gregory Anthony Compact multispectral X-ray source
US6850804B2 (en) * 2002-01-18 2005-02-01 Calfacior Corporation System method and apparatus for localized heating of tissue
US7048756B2 (en) * 2002-01-18 2006-05-23 Apasara Medical Corporation System, method and apparatus for evaluating tissue temperature
US6993394B2 (en) 2002-01-18 2006-01-31 Calfacion Corporation System method and apparatus for localized heating of tissue
US7180981B2 (en) * 2002-04-08 2007-02-20 Nanodynamics-88, Inc. High quantum energy efficiency X-ray tube and targets
US6661875B2 (en) 2002-05-09 2003-12-09 Spire Corporation Catheter tip x-ray source
DE10251635A1 (en) * 2002-11-06 2004-05-27 Feinfocus Röntgen-Systeme GmbH X-ray tube, in particular micro-focus X-ray tube
US6847164B2 (en) * 2002-12-10 2005-01-25 Applied Matrials, Inc. Current-stabilizing illumination of photocathode electron beam source
US7158612B2 (en) * 2003-02-21 2007-01-02 Xoft, Inc. Anode assembly for an x-ray tube
US6819741B2 (en) * 2003-03-03 2004-11-16 Varian Medical Systems Inc. Apparatus and method for shaping high voltage potentials on an insulator
US7447298B2 (en) * 2003-04-01 2008-11-04 Cabot Microelectronics Corporation Decontamination and sterilization system using large area x-ray source
US7563222B2 (en) * 2004-02-12 2009-07-21 Neovista, Inc. Methods and apparatus for intraocular brachytherapy
US7200203B2 (en) * 2004-04-06 2007-04-03 Duke University Devices and methods for targeting interior cancers with ionizing radiation
US7142639B2 (en) * 2004-04-19 2006-11-28 Varian Medical Systems Technologies, Inc. High voltage connector for x-ray tube
CA2697845A1 (en) * 2007-09-04 2009-03-12 Thermo Niton Analyzers Llc X-ray tube with enhanced small spot cathode and methods for manufacture thereof
US9513443B2 (en) 2008-05-28 2016-12-06 John Lawrence Erb Optical fiber-fine wire conductor and connectors
US8692117B2 (en) 2008-05-28 2014-04-08 Cardia Access, Inc. Durable fine wire electrical conductor suitable for extreme environment applications
US20090299446A1 (en) * 2008-05-28 2009-12-03 Lovoi Paul A Durable fine wire lead for therapeutic electrostimulation and sensing
US20100331941A1 (en) * 2008-05-28 2010-12-30 Walsh Robert G Implantable fine wire lead for electrostimulation and sensing
US20110220408A1 (en) * 2009-02-23 2011-09-15 Walsh Robert G Electrode and connector attachments for a cylindrical glass fiber wire lead
KR20120006501A (en) * 2009-04-07 2012-01-18 미키오 다카이 X-ray generator and composite device using the same and x-ray generating method
US8663210B2 (en) 2009-05-13 2014-03-04 Novian Health, Inc. Methods and apparatus for performing interstitial laser therapy and interstitial brachytherapy
US9193313B2 (en) 2012-03-22 2015-11-24 Nuax, Inc. Methods and apparatuses involving flexible cable/guidewire/interconnects
US9025598B1 (en) 2012-03-22 2015-05-05 Nuax, Inc. Cable/guidewire/interconnects communication apparatus and methods
US9242100B2 (en) 2012-08-07 2016-01-26 Nuax, Inc. Optical fiber-fine wire lead for electrostimulation and sensing
US9520260B2 (en) * 2012-09-14 2016-12-13 The Board Of Trustees Of The Leland Stanford Junior University Photo emitter X-ray source array (PeXSA)
JP6140983B2 (en) * 2012-11-15 2017-06-07 キヤノン株式会社 Transmission type target, x-ray generating target, x-ray generating tube, x-ray x-ray generator, and, x-ray x-ray imaging apparatus
US20140146947A1 (en) * 2012-11-28 2014-05-29 Vanderbilt University Channeling x-rays

Family Cites Families (44)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1981583A (en) 1929-10-17 1934-11-20 Invex Corp Method of preserving fruits, vegetables, etc.
US2748293A (en) 1951-09-08 1956-05-29 Hartford Nat Bank & Trust Co Irradiation applicator for X-ray therapy
DE2030624B2 (en) 1970-06-22 1980-10-09 Irmgard Fischer-Elektronik Konstruktionsbuero Und Werkstaetten Fuer Elektro- Und Vakuumtechnik, 7801 Voerstetten
US3714486A (en) 1970-10-07 1973-01-30 Crary J Mc Field emission x-ray tube
DE2259382B2 (en) 1972-12-05 1976-10-28 Roentgenstrahlenquelle
US4104530A (en) 1976-04-01 1978-08-01 Thoro-Ray Inc. Dental and medical X-ray apparatus
US4104531A (en) 1976-10-04 1978-08-01 Thoro-Ray Inc. Electron beam target carrier with ceramic window for dental or medical X-ray use
NL7610948A (en) 1976-10-04 1978-04-06 Philips Nv Roentgenbuis fine structure research.
US4109154A (en) 1977-03-18 1978-08-22 Applied Radiation X-ray beam compensation
US4117334A (en) 1977-04-11 1978-09-26 Magnaflux Corporation Portable x-ray unit with self-contained voltage supply
CA1099034A (en) 1977-10-21 1981-04-07 Leonhard Taumann Electron accelerator comprising a target exposed to the electron beam
CA1139021A (en) 1978-06-21 1983-01-04 Nils J. Baecklund Method and apparatus for measuring the content or quantity of a given element by means of x-ray radiation
DK147778C (en) 1981-12-29 1985-05-20 Andrex Radiation Prod As Roentgenstraalegenerator
US4662368A (en) 1983-06-13 1987-05-05 Trimedyne Laser Systems, Inc. Localized heat applying medical device
US4773413A (en) 1983-06-13 1988-09-27 Trimedyne Laser Systems, Inc. Localized heat applying medical device
US4517472A (en) 1983-07-06 1985-05-14 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration High voltage power supply
US4646338A (en) 1983-08-01 1987-02-24 Kevex Corporation Modular portable X-ray source with integral generator
US4606061A (en) 1983-12-28 1986-08-12 Tokyo Shibaura Denki Kabushiki Kaisha Light controlled x-ray scanner
JPS61140042A (en) 1984-12-11 1986-06-27 Hamamatsu Photonics Kk Reflecting type x-ray generating tube
JPH0550698B2 (en) 1984-12-11 1993-07-29 Hamamatsu Photonics Kk
JPS61140040A (en) 1984-12-11 1986-06-27 Hamamatsu Photonics Kk Time calibration method for x-ray streak tube
US4608997A (en) 1985-01-25 1986-09-02 Becton, Dickinson And Company Blood collection assembly
US4694480A (en) 1985-07-30 1987-09-15 Kevex Corporation Hand held precision X-ray source
US4821305A (en) 1986-03-25 1989-04-11 Varian Associates, Inc. Photoelectric X-ray tube
US4856036A (en) 1986-05-15 1989-08-08 Xi Tech Inc. Method for production of fluoroscopic and radiographic x-ray images and hand held diagnostic apparatus incorporating the same
DK336486D0 (en) 1986-07-15 1986-07-15 Andrex Radiation Prod As Coupling to spaendingsforsyning of an X-ray
DE3882482T2 (en) 1987-04-27 1994-02-03 Elekta Instr Ab Stockholm The marking device of a surgical site.
US4924485A (en) 1987-09-22 1990-05-08 Hoeberling Robert F Portable radiography system using a relativistic electron beam
US4852567A (en) 1988-01-21 1989-08-01 C. R. Bard, Inc. Laser tipped catheter
US5042058A (en) 1989-03-22 1991-08-20 University Of California Ultrashort time-resolved x-ray source
US4921327A (en) 1989-05-24 1990-05-01 Zito Richard R Method of transmitting an ionizing radiation
JPH03251263A (en) 1990-03-01 1991-11-08 Nec Corp Laser device for medical treatment
US5147353A (en) 1990-03-23 1992-09-15 Myriadlase, Inc. Medical method for applying high energy light and heat for gynecological sterilization procedures
JPH03285239A (en) * 1990-03-30 1991-12-16 Shimadzu Corp X-ray tube device
US5428658A (en) * 1994-01-21 1995-06-27 Photoelectron Corporation X-ray source with flexible probe
US5153900A (en) 1990-09-05 1992-10-06 Photoelectron Corporation Miniaturized low power x-ray source
US5090043A (en) 1990-11-21 1992-02-18 Parker Micro-Tubes, Inc. X-ray micro-tube and method of use in radiation oncology
US5116345A (en) 1990-11-28 1992-05-26 Ohio Medical Instrument Co., Inc. Stereotactically implanting an intracranial device
DE69232712D1 (en) 1991-04-05 2002-09-05 Indigo Med Inc Device with laser light transmitting needle
US5165093A (en) 1992-03-23 1992-11-17 The Titan Corporation Interstitial X-ray needle
DE4425683C2 (en) * 1994-07-20 1998-01-22 Siemens Ag Electron generating device of an X-ray tube with a cathode and with an electrode system for accelerating the electrons emitted by the cathode
US5729583A (en) 1995-09-29 1998-03-17 The United States Of America As Represented By The Secretary Of Commerce Miniature x-ray source
US5768337A (en) * 1996-07-30 1998-06-16 Varian Associates, Inc. Photoelectric X-ray tube with gain
US6111932A (en) * 1998-12-14 2000-08-29 Photoelectron Corporation Electron beam multistage accelerator

Cited By (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7220225B2 (en) 2001-02-22 2007-05-22 Retinalabs, Inc. Intraocular radiotherapy treatment
US7223225B2 (en) 2001-02-22 2007-05-29 Retinalabs, Inc. Intraocular radiotherapy treatment for macular degeneration
US6875165B2 (en) 2001-02-22 2005-04-05 Retinalabs, Inc. Method of radiation delivery to the eye
US20060142629A1 (en) * 2001-02-22 2006-06-29 Dejuan Eugene Jr Intraocular radiotherapy treatment for macular degeneration
US8100818B2 (en) 2001-02-22 2012-01-24 TDH Partners, Inc. Beta radiotherapy emitting surgical device and methods of use thereof
US20020115902A1 (en) * 2001-02-22 2002-08-22 Dejuan Eugene Beta radiotherapy emitting surgical device and methods of use thereof
US20060233307A1 (en) * 2001-06-19 2006-10-19 Mark Dinsmore X-ray source for materials analysis systems
WO2002103743A1 (en) * 2001-06-19 2002-12-27 Photoelectron Corporation X-RAY SOURCE FOR MATERIALS ANALYSIS SYSTEMs
US7526068B2 (en) 2001-06-19 2009-04-28 Carl Zeiss Ag X-ray source for materials analysis systems
JP2006524881A (en) * 2003-01-16 2006-11-02 カールツァイスシュティフトゥング、ディー/ビー/エイ カールツァイス、オーバーコーへン、ジャーマニー Thermally regulated by a field emission cathode and beam current measurement techniques
US7803102B2 (en) 2004-02-12 2010-09-28 Neovista, Inc. Methods and apparatus for intraocular brachytherapy
US8365721B2 (en) 2004-02-12 2013-02-05 Neovista Inc. Methods and apparatus for intraocular brachytherapy
US7951060B2 (en) 2004-02-12 2011-05-31 Neovista, Inc. Methods and apparatus for intraocular brachytherapy
US7744520B2 (en) 2004-02-12 2010-06-29 Neovista, Inc. Method and apparatus for intraocular brachytherapy
US20070055089A1 (en) * 2004-02-12 2007-03-08 Larsen Charles E Methods and apparatus for intraocular brachytherapy
US7803103B2 (en) 2005-02-11 2010-09-28 Neovista Inc. Methods and apparatus for intraocular brachytherapy
US8292795B2 (en) 2005-02-11 2012-10-23 Neovista, Inc. Methods and apparatus for intraocular brachytherapy
US20060258895A1 (en) * 2005-05-12 2006-11-16 Siemens Aktiengesellschaft Catheter, catheter device and imaging diagnostic apparatus
US20100094266A1 (en) * 2007-04-04 2010-04-15 The Regents Of The University Of California Laser activated micro accelerator platform
GB2446505A (en) * 2008-02-05 2008-08-13 Gen Electric X-ray generation using a secondary emission electron source
US8353812B2 (en) 2008-06-04 2013-01-15 Neovista, Inc. Handheld radiation delivery system
WO2014152515A1 (en) * 2013-03-15 2014-09-25 Varian Medical Systems, Inc. Energy degrader for radiation therapy system

Also Published As

Publication number Publication date Type
EP1208582A1 (en) 2002-05-29 application
EP1208582A4 (en) 2003-01-29 application
WO2000070645A1 (en) 2000-11-23 application
US6320932B2 (en) 2001-11-20 grant
WO2000070645A8 (en) 2001-03-29 application
US6195411B1 (en) 2001-02-27 grant

Similar Documents

Publication Publication Date Title
US4726046A (en) X-ray and electron radiotherapy clinical treatment machine
US6187037B1 (en) Metal stent containing radioactivatable isotope and method of making same
US5575749A (en) Ultra-thin high dose radioactive source wire
US6030333A (en) Implantable radiotherapy device
EP0633041A1 (en) Medical appliances for the treatment of blood vessels by means of ionizing radiation
US6419621B1 (en) Coiled brachytherapy device
US20090080602A1 (en) Dedicated breast radiation imaging/therapy system
US7070327B2 (en) Focused radiation visualization
US20070191668A1 (en) Tissue irradiation with shielding
US5531662A (en) Dual mode microwave/ionizing probe
US20030048875A1 (en) Radiation applying apparatus
US20100008469A1 (en) Elongated lifetime x-ray method and apparatus used in conjunction with a charged particle cancer therapy system
US20090076494A1 (en) Transurethral systems and methods for ablation treatment of prostate tissue
US20070108922A1 (en) Proton accelerator complex for radio-isotopes and therapy
US6496561B1 (en) Devices, methods and systems for delivery of X-ray
US6853704B2 (en) System providing multiple focused radiation beams
US6108402A (en) Diamond vacuum housing for miniature x-ray device
US20100008468A1 (en) Charged particle cancer therapy x-ray method and apparatus
US20070248214A1 (en) Energy monitoring target for x-ray dose-rate control
US5445150A (en) Invasive system employing a radiofrequency tracking system
US6910999B2 (en) Miniature x-ray unit
US6036631A (en) Device and method for intracavitary cancer treatment
US5418372A (en) Intraoperative electron beam therapy system and facility
US6415016B1 (en) Crystal quartz insulating shell for X-ray catheter
US20080281142A1 (en) Methods for asymmetrical irradiation of a body cavity

Legal Events

Date Code Title Description
AS Assignment

Owner name: PYC CORPORATION, GREECE

Free format text: SECURITY AGREEMENT;ASSIGNOR:PHOTOELECTRON CORPORATION;REEL/FRAME:013705/0362

Effective date: 20030121

AS Assignment

Owner name: CARL-ZEISS-STIFTUNG DOING BUSINESS AS CARL ZEISS,

Free format text: ASSET PURCHASE AGREEMENT;ASSIGNOR:PHOTOELECTRON CORPORATION;REEL/FRAME:014981/0591

Effective date: 20030604

RF Reissue application filed

Effective date: 20031120

FPAY Fee payment

Year of fee payment: 4

AS Assignment

Owner name: CARL ZEISS AG, GERMANY

Free format text: CHANGE OF NAME;ASSIGNOR:CARL-ZEISS-STIFTUING DOING BUSINESS AS ZEISS, CARL;REEL/FRAME:017555/0001

Effective date: 20040420

FPAY Fee payment

Year of fee payment: 8

FPAY Fee payment

Year of fee payment: 12