CA2090210C - Interstitial x-ray needle - Google Patents
Interstitial x-ray needle Download PDFInfo
- Publication number
- CA2090210C CA2090210C CA002090210A CA2090210A CA2090210C CA 2090210 C CA2090210 C CA 2090210C CA 002090210 A CA002090210 A CA 002090210A CA 2090210 A CA2090210 A CA 2090210A CA 2090210 C CA2090210 C CA 2090210C
- Authority
- CA
- Canada
- Prior art keywords
- tube
- casing
- tip
- needle
- chamber
- 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.)
- Expired - Fee Related
Links
- 239000002826 coolant Substances 0.000 claims abstract description 16
- 230000005291 magnetic effect Effects 0.000 claims abstract description 9
- 206010028980 Neoplasm Diseases 0.000 claims description 7
- 210000001519 tissue Anatomy 0.000 description 4
- 230000005855 radiation Effects 0.000 description 3
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 3
- 201000011510 cancer Diseases 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000003780 insertion Methods 0.000 description 2
- 230000037431 insertion Effects 0.000 description 2
- 229920000136 polysorbate Polymers 0.000 description 2
- 239000002356 single layer Substances 0.000 description 2
- 238000002560 therapeutic procedure Methods 0.000 description 2
- 238000004804 winding Methods 0.000 description 2
- 229910052729 chemical element Inorganic materials 0.000 description 1
- 238000010894 electron beam technology Methods 0.000 description 1
- 230000035876 healing Effects 0.000 description 1
- 230000002977 hyperthermial effect Effects 0.000 description 1
- 239000012212 insulator Substances 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000001959 radiotherapy Methods 0.000 description 1
- 210000004872 soft tissue Anatomy 0.000 description 1
- 230000002195 synergetic effect Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
- H01J35/14—Arrangements for concentrating, focusing, or directing the cathode ray
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/32—Tubes wherein the X-rays are produced at or near the end of the tube or a part thereof which tube or part has a small cross-section to facilitate introduction into a small hole or cavity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N5/1027—Interstitial radiation therapy
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J2235/00—X-ray tubes
- H01J2235/12—Cooling
- H01J2235/1204—Cooling of the anode
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J2235/00—X-ray tubes
- H01J2235/12—Cooling
- H01J2235/1225—Cooling characterised by method
- H01J2235/1262—Circulating fluids
Abstract
An interstitial X-ray needle includes an elongated X-ray tube coupled to an electron emitter at one end of the tube, with a converter element being dis-posed at a tip of the other end of the tube for converting emitted electrons into X-rays; a solenoid coil wound around the tube for providing a magnetic field that confines the emitted electrons within a narrow beam; an elongated outer casing enclosing the tube and coil; and a pipe coaxially disposed between the casing and the tube for defining an inner annular flow chamber between the tip of the tube and a coolant inlet in the casing and an outer annular flow chamber between the tip of the tube and a coolant outlet in the casing.
Description
2p~~f Z1U
BACKGROUND OF THE INVENTION
The present invenUon generally pertains to X-ray apparatus and is par-ticularly directed to an interstitial X-ray needle.
An X-ray apparatus is used for radiation therapy of cancer patients. One such apparatus, as described in United States Patent No. 2,748.293 to Reiniger, includes an elongated X-ray tube with a converter element being disposed at a tip of the tube for converting emitted electrons into X-rays; and an elongated outer casing enclosing the tube and deeming a coolant flow chamber through which coolant may flow to transfer heat from the tip of the tube. The tube is inserted into a cancer patient's body through a body cavity to position the converter ele-ment so that the X-rays can be concentrated at the tumor and thereby minimize radiation damage to ad)acent undiseased tissue. However, the size of such an X-ray apparatus is too large for insertion of the tube through the skin, whereby the applicability of X-ray therapy for treatment of cancerous internal body parts has been limited to only those body parts that can be accessed through body cavities.
SUMMARY OP' THE INVENTION
The present invention provides an interstitial X-ray needle, comprising an elongated X-ray tube coupled to an electron emitter at one end of the tube, with a converter element being disposed at a tip of the other end of the tube for converting emitted electrons into X-rays: a solenoid coil wound around the tube for providing a magnetic field that confines the emitted electrons within a narrow beam; an elongated outer casing enclosing the tube and coil; and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube.
-i-The intersti~:ial X-ray needle of the present invention may be of suwr~ small diameter that a portion of the casing extending at least approximately five centimeters from the tip of the tu:oe has a maximum outside diameter of approximately two millimeters. An X-ray needle of such small diameter may be :~rcserted in a patient's body without significant damage to tissue between the skin and the tumor site, thereby significantly increasing the applicability of X-ray therapy for treatment of cancerous internal body parts.
To prevent electron loss and stray X-radiation, the solenoid coil is wound around the beam-transport tube in order to provide a magnetic field that tightly confines the emitted electrons.
In accordance with the present invention, there is provided an interstitia:~ X-ray needle, comprising an elongated X-ray tube coupled t:o an electron emitter at one end of the tube, with a converter element being disposed at a tip of the other ena of the tube for converting emitted electrons into X-rays; a solenoid coil wound around the tube for providing a magnetir_ field that confines the emitted electrons within a narrow beam; an elongated outer casing enclosing the tube and. coil; and means within the casing defining coolant flow czambers for directing coolant to and from the tip of the tube; wherein the needle is of such small diameter that tree needle may be inserted in a patient's body without: significant damage to tissue between the skin and a tumor :>i t.e .
In accordance with the present invention, there is further provided an i~-Lterstitial X-ray needle, comprising an elongated X-ray tube coupled to an ei~ectron emitter at one end of the tube, with a converter element being disposed at a tip of the other end of the tube for converting emitted electrons into X-rays; a solenoid coil wound around the tube for providing a magnet:i.c field that: confines the emitted electrons within a narrow beam; an elongated outer casing enclosing the tube and coil, wherein a portion of the casing extending at least appa-aximately five centimeters from the tip of the tube has a maximum outside diameter of approximately two millimeters; and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube.
In one aspect of the present invention, the coolant-flow-chamber-defining means comprises a pipe coaxially disposed between the casing and the tube for defining an inner annu:rar flow charnber between the tip of the tube and a first opening in the casing and an outer annular flow chamber between the tip of the tube and a second opening in the easing.
In another aspect: of the present invention, the coolant-flow-chamber-defining means comprises a plurality of pipes disposed between the casing and the tube wherein each pipe defines an input low chamber between the tip of the tube and at least one :inlet opening in the casing and wherein the space between the tube and the casing not occupied by the pipes defines an output flow chamber between the tip of the tube and an outlet opening in the casing.
Additional features of the present invention are described in relation to the description of the preferred embodiment.
-2a-2(~90~~ ~
BRIIw:F' DESCRIPTION OF' THE DRAWING
Figure 1 is a diagram of an X-ray apparatus including a preferred em-bodirnent of the interstitial X-ray needle of the present invention.
Figure 2 is a sectional view of the needle of Figure 1 taken along lines z-2.
Figure 3 is a diagram of a portion of the needle illustrating an alternative preferred embodiment of the flow-chamber defining means.
Figure 4 is a sectional view of the needle of Figure 3 taken along lines 4-4.
DESCRIPTION OP' THE PREFERRED EMBODIMENTS
Referring to Figures 1 and 2, an X-ray apparatus containing a preferred embodiment of the Interstitial X-ray needle of the present invention includes the needle 10 and a diode housing 12 for receiving the needle. The diode housing includes a vacuum chamber 14 containing an electron emitter 16 and a control grid 18. The electron emitter 16 is connected to a high voltage cable 20, which is connected to a high voltage source (not shown). Insulators 22 are stacked be-tween the electron emitter 16 and the diode housing 12.
The needle 10 includes an elongated X-ray tube 24, a converter element 26, a solenoid coil 28, an elongated outer casing 30 and a pipe 32.
The X-ray tube 24 has an open end 34 which opens into the vacuum chamber 14 to couple the X-ray tube 24 to the electron emitter 16.
BACKGROUND OF THE INVENTION
The present invenUon generally pertains to X-ray apparatus and is par-ticularly directed to an interstitial X-ray needle.
An X-ray apparatus is used for radiation therapy of cancer patients. One such apparatus, as described in United States Patent No. 2,748.293 to Reiniger, includes an elongated X-ray tube with a converter element being disposed at a tip of the tube for converting emitted electrons into X-rays; and an elongated outer casing enclosing the tube and deeming a coolant flow chamber through which coolant may flow to transfer heat from the tip of the tube. The tube is inserted into a cancer patient's body through a body cavity to position the converter ele-ment so that the X-rays can be concentrated at the tumor and thereby minimize radiation damage to ad)acent undiseased tissue. However, the size of such an X-ray apparatus is too large for insertion of the tube through the skin, whereby the applicability of X-ray therapy for treatment of cancerous internal body parts has been limited to only those body parts that can be accessed through body cavities.
SUMMARY OP' THE INVENTION
The present invention provides an interstitial X-ray needle, comprising an elongated X-ray tube coupled to an electron emitter at one end of the tube, with a converter element being disposed at a tip of the other end of the tube for converting emitted electrons into X-rays: a solenoid coil wound around the tube for providing a magnetic field that confines the emitted electrons within a narrow beam; an elongated outer casing enclosing the tube and coil; and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube.
-i-The intersti~:ial X-ray needle of the present invention may be of suwr~ small diameter that a portion of the casing extending at least approximately five centimeters from the tip of the tu:oe has a maximum outside diameter of approximately two millimeters. An X-ray needle of such small diameter may be :~rcserted in a patient's body without significant damage to tissue between the skin and the tumor site, thereby significantly increasing the applicability of X-ray therapy for treatment of cancerous internal body parts.
To prevent electron loss and stray X-radiation, the solenoid coil is wound around the beam-transport tube in order to provide a magnetic field that tightly confines the emitted electrons.
In accordance with the present invention, there is provided an interstitia:~ X-ray needle, comprising an elongated X-ray tube coupled t:o an electron emitter at one end of the tube, with a converter element being disposed at a tip of the other ena of the tube for converting emitted electrons into X-rays; a solenoid coil wound around the tube for providing a magnetir_ field that confines the emitted electrons within a narrow beam; an elongated outer casing enclosing the tube and. coil; and means within the casing defining coolant flow czambers for directing coolant to and from the tip of the tube; wherein the needle is of such small diameter that tree needle may be inserted in a patient's body without: significant damage to tissue between the skin and a tumor :>i t.e .
In accordance with the present invention, there is further provided an i~-Lterstitial X-ray needle, comprising an elongated X-ray tube coupled to an ei~ectron emitter at one end of the tube, with a converter element being disposed at a tip of the other end of the tube for converting emitted electrons into X-rays; a solenoid coil wound around the tube for providing a magnet:i.c field that: confines the emitted electrons within a narrow beam; an elongated outer casing enclosing the tube and coil, wherein a portion of the casing extending at least appa-aximately five centimeters from the tip of the tube has a maximum outside diameter of approximately two millimeters; and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube.
In one aspect of the present invention, the coolant-flow-chamber-defining means comprises a pipe coaxially disposed between the casing and the tube for defining an inner annu:rar flow charnber between the tip of the tube and a first opening in the casing and an outer annular flow chamber between the tip of the tube and a second opening in the easing.
In another aspect: of the present invention, the coolant-flow-chamber-defining means comprises a plurality of pipes disposed between the casing and the tube wherein each pipe defines an input low chamber between the tip of the tube and at least one :inlet opening in the casing and wherein the space between the tube and the casing not occupied by the pipes defines an output flow chamber between the tip of the tube and an outlet opening in the casing.
Additional features of the present invention are described in relation to the description of the preferred embodiment.
-2a-2(~90~~ ~
BRIIw:F' DESCRIPTION OF' THE DRAWING
Figure 1 is a diagram of an X-ray apparatus including a preferred em-bodirnent of the interstitial X-ray needle of the present invention.
Figure 2 is a sectional view of the needle of Figure 1 taken along lines z-2.
Figure 3 is a diagram of a portion of the needle illustrating an alternative preferred embodiment of the flow-chamber defining means.
Figure 4 is a sectional view of the needle of Figure 3 taken along lines 4-4.
DESCRIPTION OP' THE PREFERRED EMBODIMENTS
Referring to Figures 1 and 2, an X-ray apparatus containing a preferred embodiment of the Interstitial X-ray needle of the present invention includes the needle 10 and a diode housing 12 for receiving the needle. The diode housing includes a vacuum chamber 14 containing an electron emitter 16 and a control grid 18. The electron emitter 16 is connected to a high voltage cable 20, which is connected to a high voltage source (not shown). Insulators 22 are stacked be-tween the electron emitter 16 and the diode housing 12.
The needle 10 includes an elongated X-ray tube 24, a converter element 26, a solenoid coil 28, an elongated outer casing 30 and a pipe 32.
The X-ray tube 24 has an open end 34 which opens into the vacuum chamber 14 to couple the X-ray tube 24 to the electron emitter 16.
2~90~~~J
The converter element 26 is disposed at a tip 36 of the other end of the tube 24 for converting electrons emitted from the electron emitter 16 into X-rays.
The solenoid coil 28 is wound around the tube 24 for providing a mag-netic field that confines the emitted electrons within a narrow beam. The electron beam can be confined to a diameter of approximately 0.4 millimeter when the solenoid coil 28 provides a magnetic field of approximately 20 gauss. For a coil 28 having 13 ohms resistance and wound at 20 turns-per-centimeter, the required current in the winding is only 0.8 amperes and the required voltage across the coil is only O.1 volts, whereby the power expended in the winding is only 0.08 watts.
The outer casing 30 encloses the tube 24 and coil 28.
The pipe 32 is coaxially disposed between the outer casing 30 and the tube 24 for defining an inner annular flow channel 38 between the tip 36 of the tube 24 and a coolant inlet 40 in the casing 30, and an outer annular flow cham-ber 42 between the tip 36 of the tube 24 and a coolant outlet 44 in the casing 30.
For a needle 10 of the embodirnent of Figures 1 and 2, including a ten-centimeter long tube 24 having an inside diameter of 0.64 millimeter and an out-side diameter of 0.81 millimeter wound with a single layer of #33 magnetic wire of 0.22 millimeter diameter at approximately 40 turns-per-centimeter, an outer casing 30 having an outside diameter of 2.8 millimeters and an inside diameter of 2.16 millimeters, and a pipe of 1.52 millimeters inside diameter and 1.83 mil-limeters outside diameter, a water flow rate of 87 milliliters-per-minute is obtained at an inlet pressure of 20 pounds-per-square-inch, whereby for a 20 watt heat rate at the tip 36 of the needle 10, the water temperature rise over ten minutes is less than 5 degrees Celsius.
The converter element 26 is disposed at a tip 36 of the other end of the tube 24 for converting electrons emitted from the electron emitter 16 into X-rays.
The solenoid coil 28 is wound around the tube 24 for providing a mag-netic field that confines the emitted electrons within a narrow beam. The electron beam can be confined to a diameter of approximately 0.4 millimeter when the solenoid coil 28 provides a magnetic field of approximately 20 gauss. For a coil 28 having 13 ohms resistance and wound at 20 turns-per-centimeter, the required current in the winding is only 0.8 amperes and the required voltage across the coil is only O.1 volts, whereby the power expended in the winding is only 0.08 watts.
The outer casing 30 encloses the tube 24 and coil 28.
The pipe 32 is coaxially disposed between the outer casing 30 and the tube 24 for defining an inner annular flow channel 38 between the tip 36 of the tube 24 and a coolant inlet 40 in the casing 30, and an outer annular flow cham-ber 42 between the tip 36 of the tube 24 and a coolant outlet 44 in the casing 30.
For a needle 10 of the embodirnent of Figures 1 and 2, including a ten-centimeter long tube 24 having an inside diameter of 0.64 millimeter and an out-side diameter of 0.81 millimeter wound with a single layer of #33 magnetic wire of 0.22 millimeter diameter at approximately 40 turns-per-centimeter, an outer casing 30 having an outside diameter of 2.8 millimeters and an inside diameter of 2.16 millimeters, and a pipe of 1.52 millimeters inside diameter and 1.83 mil-limeters outside diameter, a water flow rate of 87 milliliters-per-minute is obtained at an inlet pressure of 20 pounds-per-square-inch, whereby for a 20 watt heat rate at the tip 36 of the needle 10, the water temperature rise over ten minutes is less than 5 degrees Celsius.
Referring to Figures 3 and 4, in an alternative preferred embodiment, the needle l0A includes an elongated X-ray tube 24, a com~erter element 26, a solenoid coil 28, an elongated outer casing 30 and a plurality of pipes 46.
'The pipes 46 are disposed between the casing 30 and the tube 24. Each pipe defines an input flow chamber 48 between the tip 36 of the tube 24 and at Ieast one inlet opening (not shown) in the casing 30: and the space 50 beriveen the tube 24 and tile casing 30 not occupied by Lhe pipes 46 defines an output now chamber be-tween the tip 36 of the tube 24 and an outlet opening (not shown) in the casing 30.
For a needle lOA of the embodiment of Figures 3 and 4, including a ten-centimeter long tube 24 having an inside diameter of 0.64 millimeter and an out-side diameter of 0.81 millimeter wound with a single layer of #33 magnetic wire of 0.22 millimeter diameter at approximately 40 turns-per-centimeter, an outer casing 30 having an outside diameter of 2.8 millimeters and an inside diameter of 2.16 millimeters, and four pipes each having outlet orifice )ets 52 of 0.15 mil-limeter directed at the tip 36 of the needle 10A, a w2ter flow rate of 10 milliliters-per-minute is obtained at an inlet pressure of 50 pounds-per-square-inch, Wll(:1'Cl)y fUl' a 20 wall heat rate at the tip 36 of the needle 10A, the water tempera-ture rise over ten minutes is approximately 28 degrees Celsius.
The tube 24, casing 30 and pipe 32 or pipes 46 typically are rigid and straight, but also may be made of flexible materials or may be curved rather than straight so as to enable insertion of the tip of the needle to portions of the body that are not directly accessible through soft tissue.
The X-ray apparatus described herein may be operated at a relatively low power level of 14 watts when delivering a radiation dose of approximately 100 Gray over' ten minutes duration to tissue located one centimeter from the con-verter element 26 by operating with an electron emater voltage of 200 kilovolts and a beam current of 0.07 milliamperes.
'The pipes 46 are disposed between the casing 30 and the tube 24. Each pipe defines an input flow chamber 48 between the tip 36 of the tube 24 and at Ieast one inlet opening (not shown) in the casing 30: and the space 50 beriveen the tube 24 and tile casing 30 not occupied by Lhe pipes 46 defines an output now chamber be-tween the tip 36 of the tube 24 and an outlet opening (not shown) in the casing 30.
For a needle lOA of the embodiment of Figures 3 and 4, including a ten-centimeter long tube 24 having an inside diameter of 0.64 millimeter and an out-side diameter of 0.81 millimeter wound with a single layer of #33 magnetic wire of 0.22 millimeter diameter at approximately 40 turns-per-centimeter, an outer casing 30 having an outside diameter of 2.8 millimeters and an inside diameter of 2.16 millimeters, and four pipes each having outlet orifice )ets 52 of 0.15 mil-limeter directed at the tip 36 of the needle 10A, a w2ter flow rate of 10 milliliters-per-minute is obtained at an inlet pressure of 50 pounds-per-square-inch, Wll(:1'Cl)y fUl' a 20 wall heat rate at the tip 36 of the needle 10A, the water tempera-ture rise over ten minutes is approximately 28 degrees Celsius.
The tube 24, casing 30 and pipe 32 or pipes 46 typically are rigid and straight, but also may be made of flexible materials or may be curved rather than straight so as to enable insertion of the tip of the needle to portions of the body that are not directly accessible through soft tissue.
The X-ray apparatus described herein may be operated at a relatively low power level of 14 watts when delivering a radiation dose of approximately 100 Gray over' ten minutes duration to tissue located one centimeter from the con-verter element 26 by operating with an electron emater voltage of 200 kilovolts and a beam current of 0.07 milliamperes.
In addition to providing benefits incident to its size, the miWature inter-stitial X-ray needle of the present invention also may generate controlled hyper-thermic temperatures for application to the treated tumor, which combined with the radiation treatment may provide a synergistic healing effect.
Claims (9)
1. An interstitial X-ray needle. comprising an elongated X-ray tube coupled to an electron emitter at one end of the tube.
with a converter element being disposed at a tip of the other end of the tube for converting emitted electrons into X-rays;
a solenoid coil wound around the tube for providing a magnetic field that confines the emitted electrons within a narrow beam;
an elongated outer casing enclosing the tube and coil: and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube:
wherein the needle is of such small diameter that the needle may be inserted in a patient's body without significant damage to tissue between the skin and a tumor site.
with a converter element being disposed at a tip of the other end of the tube for converting emitted electrons into X-rays;
a solenoid coil wound around the tube for providing a magnetic field that confines the emitted electrons within a narrow beam;
an elongated outer casing enclosing the tube and coil: and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube:
wherein the needle is of such small diameter that the needle may be inserted in a patient's body without significant damage to tissue between the skin and a tumor site.
2. A needle according to Claim 1. wherein the flow-chamber-defining means comprises a pipe coaxially disposed between the casing and the tube for defining an inner annular flow chamber between the tip of the tube and a first opening in the casing and an outer annular flow chamber between the tip of the tube and a second opening in the casing.
3. A needle according to Claim 1, wherein the flow-chamber-defining means comprises a plurality of pipes disposed between the casing and the tube wherein each pipe defines an input flow chamber between the tip of the tube and at least one inlet opening in the casing and wherein the space between the tip of the tube and the casing not occupied by the pipes defines an output flow chamber between the tip of the tube and an outlet opening in the casing.
4. A needle according to Claim 1, 2 or 3. wherein the outer casing has an outside diameter of approximately 2.8 millimeters.
5. A needle according to Claim 1, 2 or 3, wherein the narrow beam has a diameter of approximately 0.4 millimeters.
6. An interstitial X-ray needle comprising an elongated X-ray tube coupled to an electron emitter at one end of the tube, with a converter element being disposed at a tip of the other end of the tube for converting emitted electrons into x-rays;
a solenoid coil wound around the tube for providing a magnetic field that confines the emitted electrons within a narrow beam;
an elongated outer casing enclosing the tube and coil, wherein a portion of the casing extending at least approximately five centimeters from the tip of the tube has a maximum outside diameter of approximately two millimeters: and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube .
a solenoid coil wound around the tube for providing a magnetic field that confines the emitted electrons within a narrow beam;
an elongated outer casing enclosing the tube and coil, wherein a portion of the casing extending at least approximately five centimeters from the tip of the tube has a maximum outside diameter of approximately two millimeters: and means within the casing defining coolant flow chambers for directing coolant to and from the tip of the tube .
7. A needle according to Claim 6, wherein the flow-chamber-defining means comprises a pipe coaxially disposed between the casing and the tube for defining an inner annular flow chamber between the tip of the tube and a first opening in the casing and an outer annular flow chamber between the tip of the tube and a second opening in the casing.
8. A needle according to Claim 6, wherein the flow-chamber-defining means comprises a plurality of pipes disposed between the casing and the tube wherein each pipe defines an input flow chamber between the tip of the tube and at least one inlet opening in the casing and wherein the space between the tip of the tube and the casing not occupied by the pipes defines an output flow chamber between the tip of the tube and an outlet opening in the casing.
9. A needle according to Claim 6, 7 or 8, wherein the narrow beam has a diameter of approximately 0.4 millimeters.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/855,664 US5165093A (en) | 1992-03-23 | 1992-03-23 | Interstitial X-ray needle |
| US07/855,664 | 1992-03-23 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2090210A1 CA2090210A1 (en) | 1993-09-24 |
| CA2090210C true CA2090210C (en) | 2002-07-16 |
Family
ID=25321797
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002090210A Expired - Fee Related CA2090210C (en) | 1992-03-23 | 1993-02-23 | Interstitial x-ray needle |
Country Status (6)
| Country | Link |
|---|---|
| US (2) | US5165093A (en) |
| EP (1) | EP0562759B1 (en) |
| JP (1) | JPH06142220A (en) |
| CA (1) | CA2090210C (en) |
| DE (1) | DE69311415T2 (en) |
| DK (1) | DK0562759T3 (en) |
Families Citing this family (76)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4985832A (en) * | 1986-09-18 | 1991-01-15 | Digital Equipment Corporation | SIMD array processing system with routing networks having plurality of switching stages to transfer messages among processors |
| 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 |
| US5428658A (en) * | 1994-01-21 | 1995-06-27 | Photoelectron Corporation | X-ray source with flexible probe |
| DE69523457D1 (en) * | 1994-07-12 | 2001-11-29 | Photoelectron Corp | X-RAY RADIATOR FOR DOSING A PREDICTED RADIATION FLOW ON THE INNER SURFACES OF BODY CAVES |
| 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 |
| FR2728472B1 (en) * | 1994-12-27 | 1997-03-28 | Ge Medical Syst Sa | RADIATION THERAPY APPARATUS USING A HIGH FREQUENCY LINEAR ELECTRON ACCELERATOR AND NON-FIELD PROTECTIVE MEANS |
| US6377846B1 (en) | 1997-02-21 | 2002-04-23 | Medtronic Ave, Inc. | Device for delivering localized x-ray radiation and method of manufacture |
| EP0847249A4 (en) | 1995-08-24 | 2004-09-29 | Medtronic Ave Inc | X-ray catheter |
| US5729583A (en) * | 1995-09-29 | 1998-03-17 | The United States Of America As Represented By The Secretary Of Commerce | Miniature x-ray source |
| AU726908B2 (en) * | 1995-10-09 | 2000-11-23 | Otsuka Pharmaceutical Co., Ltd. | Breath sampling bag and gas measuring apparatus |
| DK1380258T3 (en) * | 1995-10-09 | 2006-03-13 | Otsuka Pharma Co Ltd | Respiratory test bag and gas measuring equipment |
| US5689542A (en) * | 1996-06-06 | 1997-11-18 | Varian Associates, Inc. | X-ray generating apparatus with a heat transfer device |
| US5737384A (en) * | 1996-10-04 | 1998-04-07 | Massachusetts Institute Of Technology | X-ray needle providing heating with microwave energy |
| EP0860181B1 (en) * | 1997-02-21 | 2004-04-28 | Medtronic Ave, Inc. | X-ray device having a dilatation structure for delivering localized radiation to an interior of a body |
| US5854822A (en) * | 1997-07-25 | 1998-12-29 | Xrt Corp. | Miniature x-ray device having cold cathode |
| US6108402A (en) * | 1998-01-16 | 2000-08-22 | Medtronic Ave, Inc. | Diamond vacuum housing for miniature x-ray device |
| US6069938A (en) * | 1998-03-06 | 2000-05-30 | Chornenky; Victor Ivan | Method and x-ray device using pulse high voltage source |
| US6134295A (en) * | 1998-10-29 | 2000-10-17 | University Of New Mexico | Apparatus using a x-ray source for radiation therapy port verification |
| US6249569B1 (en) * | 1998-12-22 | 2001-06-19 | General Electric Company | X-ray tube having increased cooling capabilities |
| US6289079B1 (en) | 1999-03-23 | 2001-09-11 | Medtronic Ave, Inc. | X-ray device and deposition process for manufacture |
| US6195411B1 (en) | 1999-05-13 | 2001-02-27 | Photoelectron Corporation | Miniature x-ray source with flexible probe |
| US6353658B1 (en) | 1999-09-08 | 2002-03-05 | The Regents Of The University Of California | Miniature x-ray source |
| AU2738001A (en) * | 1999-12-28 | 2001-07-09 | Apple, Marc G. | Enhanced energy radiotherapy balloon catheter |
| WO2001054761A2 (en) | 2000-01-28 | 2001-08-02 | William Cook, Europe Aps | Endovascular medical device with plurality of wires |
| US6421416B1 (en) | 2000-02-11 | 2002-07-16 | Photoelectron Corporation | Apparatus for local radiation therapy |
| US6301328B1 (en) | 2000-02-11 | 2001-10-09 | Photoelectron Corporation | Apparatus for local radiation therapy |
| US7109505B1 (en) | 2000-02-11 | 2006-09-19 | Carl Zeiss Ag | Shaped biocompatible radiation shield and method for making same |
| US6285735B1 (en) | 2000-02-11 | 2001-09-04 | Photoelectron Corporation | Apparatus for local radiation therapy |
| US6546080B1 (en) * | 2000-11-10 | 2003-04-08 | Scimed Life Systems, Inc. | Heat sink for miniature x-ray unit |
| 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 |
| 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 |
| US6540720B1 (en) | 2000-11-10 | 2003-04-01 | Scimed Life Systems, Inc. | Miniature x-ray unit |
| EP1217642A1 (en) * | 2000-12-22 | 2002-06-26 | Radi Medical Technologies AB | Active cooling of a miniature x-ray tube |
| US6521350B2 (en) * | 2001-06-18 | 2003-02-18 | Alfred E. Mann Foundation For Scientific Research | Application and manufacturing method for a ceramic to metal seal |
| US6661876B2 (en) * | 2001-07-30 | 2003-12-09 | Moxtek, Inc. | Mobile miniature X-ray source |
| 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 |
| MXPA05001567A (en) * | 2002-08-14 | 2005-04-25 | Gw Pharma Ltd | Cannabinoid liquid formulations for mucosal amdinistration. |
| AU2003272381A1 (en) * | 2002-09-13 | 2004-04-30 | Moxtek, Inc. | Radiation window and method of manufacture |
| US7158612B2 (en) * | 2003-02-21 | 2007-01-02 | Xoft, Inc. | Anode assembly for an x-ray tube |
| EP1493466B1 (en) * | 2003-06-30 | 2012-06-20 | Nucletron Operations B.V. | Miniature X-ray source with cryogenic cooling |
| 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 |
| US20080021257A1 (en) * | 2006-07-18 | 2008-01-24 | Ams Research Corporation | X-Ray Brachytherapy System and Device |
| US7737424B2 (en) * | 2007-06-01 | 2010-06-15 | Moxtek, Inc. | X-ray window with grid structure |
| 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 |
| US20100285271A1 (en) | 2007-09-28 | 2010-11-11 | Davis Robert C | Carbon nanotube assembly |
| US9305735B2 (en) | 2007-09-28 | 2016-04-05 | Brigham Young University | Reinforced polymer x-ray window |
| US8498381B2 (en) | 2010-10-07 | 2013-07-30 | Moxtek, Inc. | Polymer layer on X-ray window |
| US7965818B2 (en) * | 2008-07-01 | 2011-06-21 | Minnesota Medical Physics Llc | Field emission X-ray apparatus, methods, and systems |
| 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 |
| DE102010032338B4 (en) * | 2010-07-27 | 2017-08-24 | X-Ray Worx Gmbh | Microfocus X-ray tube |
| 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 |
| 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 |
| US9174412B2 (en) | 2011-05-16 | 2015-11-03 | Brigham Young University | High strength carbon fiber composite wafers for microfabrication |
| 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 |
| JP5804777B2 (en) * | 2011-06-01 | 2015-11-04 | キヤノン株式会社 | X-ray generator tube and X-ray generator |
| 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 |
| GB2502109A (en) * | 2012-05-16 | 2013-11-20 | Ariane Medical Systems Ltd | X-ray radiotherapy apparatus with indirectly heated emissive cathode |
| US9072154B2 (en) | 2012-12-21 | 2015-06-30 | Moxtek, Inc. | Grid voltage generation for x-ray tube |
| 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 |
| US9173623B2 (en) | 2013-04-19 | 2015-11-03 | Samuel Soonho Lee | X-ray tube and receiver inside mouth |
| DE102018114000B4 (en) * | 2018-06-12 | 2020-06-10 | Carl Zeiss Meditec Ag | Medical radiation therapy system and method for operating the same |
Family Cites Families (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE710118C (en) * | 1938-02-26 | 1941-09-04 | Dr Marius Kratzenstein | Hollow anode tube with magnetic shield |
| US2356645A (en) * | 1943-02-08 | 1944-08-22 | Gen Electric X Ray Corp | X-ray tube |
| US2362816A (en) * | 1943-04-15 | 1944-11-14 | Gen Electric | Electrical discharge device |
| GB701050A (en) * | 1950-03-22 | 1953-12-16 | Werner Ehrenberg | Improvements in or relating to x-ray tubes |
| US2748293A (en) * | 1951-09-08 | 1956-05-29 | Hartford Nat Bank & Trust Co | Irradiation applicator for X-ray therapy |
| US3609432A (en) * | 1968-11-08 | 1971-09-28 | Rigaku Denki Co Ltd | Thin target x-ray tube with means for protecting the target |
| US3668454A (en) * | 1969-08-05 | 1972-06-06 | Rigaku Denki Co Ltd | Fine focus x-ray tube |
| US3783251A (en) * | 1970-11-27 | 1974-01-01 | Varian Associates | Computer assisted radiation therapy machine |
| US3969629A (en) * | 1975-03-14 | 1976-07-13 | Varian Associates | X-ray treatment machine having means for reducing secondary electron skin dose |
| CA1099034A (en) * | 1977-10-21 | 1981-04-07 | Leonhard Taumann | Electron accelerator comprising a target exposed to the electron beam |
| JPS5725863A (en) * | 1980-07-23 | 1982-02-10 | Olympus Optical Co | Endoscope with microwave heater |
| EP0165993A1 (en) * | 1983-12-27 | 1986-01-02 | The Board Of Trustees Of The Leland Stanford Junior University | Catheter for treatment of tumors and method for using same |
| JPH0511882Y2 (en) * | 1987-01-06 | 1993-03-25 | ||
| US4825880A (en) * | 1987-06-19 | 1989-05-02 | The Regents Of The University Of California | Implantable helical coil microwave antenna |
| US4969863A (en) * | 1988-10-28 | 1990-11-13 | Eric van't Hooft | Adaptor for remote after-loading apparatus for radiotherapy |
| US5026959A (en) * | 1988-11-16 | 1991-06-25 | Tokyo Keiki Co. Ltd. | Microwave radiator for warming therapy |
-
1992
- 1992-03-23 US US07/855,664 patent/US5165093A/en not_active Ceased
-
1993
- 1993-02-23 CA CA002090210A patent/CA2090210C/en not_active Expired - Fee Related
- 1993-03-18 DE DE69311415T patent/DE69311415T2/en not_active Expired - Fee Related
- 1993-03-18 EP EP93302049A patent/EP0562759B1/en not_active Expired - Lifetime
- 1993-03-18 DK DK93302049.7T patent/DK0562759T3/en active
- 1993-03-22 JP JP5062246A patent/JPH06142220A/en active Pending
-
1994
- 1994-07-05 US US08/270,261 patent/USRE35383E/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| DE69311415D1 (en) | 1997-07-17 |
| US5165093A (en) | 1992-11-17 |
| CA2090210A1 (en) | 1993-09-24 |
| USRE35383E (en) | 1996-11-26 |
| EP0562759A1 (en) | 1993-09-29 |
| JPH06142220A (en) | 1994-05-24 |
| DE69311415T2 (en) | 1997-10-16 |
| DK0562759T3 (en) | 1997-07-07 |
| EP0562759B1 (en) | 1997-06-11 |
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