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 disposed at a tip of the other end of the tube for converting emitted electrons into x-ray; 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.
|
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.
4. 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 electronss 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 an from the tip of the tube.
2. A needle according to
3. A needle according to
5. A needle according to
6. A needle according to
7. An interstitial x-ray needle, including,
first means for producing a plurality of electrons, second means for including a tube for directing the electrons from the first means in a particular path, third means disposed at the end of the particular path for converting the electrons to x-rays, fourth means including a casing disposed in enveloping relationship to the tube for cooling the third means, and fifth means disposed on the tube for confining the electrons to a beam during the direction of the electrons in the particular path to the third means. 8. An interstitial x-ray needle as set forth in the third means receives the electrons after the passage of the electrons in the particular path through the tube and converts the electrons to
x-rays. 9. An interstitial x-ray needle as set forth in claim 8 wherein the tube has a tip and the third means includes a converter element disposed at the tip of the tube to receive the electrons after the passage of the electrons through the first tube and to convert the received electrons to x-rays. 10. An interstitial x-ray needle as set forth in claim 9 wherein the tube and the casing are disposed in a coaxial relationship. 11. An interstitial x-ray needle as set forth in claim 7 wherein the casing envelopes the second means, the third means and the fifth means and provides for a flow of a cooling fluid past the third means to cool the third means. 12. An interstitial x-ray needle as set forth in claim 7, including, there being a space between the tube and the casing, there being at least one hollow pipe in the space between the tube and the casing, the hollow pipe being included in the fourth means for introducing fluid to the third means to cool the third means, the hollow pipe only partially occupying the space between the tube and the casing, and the remaining space between the tube and the casing providing for the flow of the cooling fluid from the third means. 13. An interstitial x-ray tube as set forth in claim 7 wherein the fifth means is operative to confine the electron beam to a diameter no greater than approximately four tenths of a millimeter (0.4 mm). 14. An interstitial x-ray tube as set forth in claim 7 wherein the casing has a width no greater than approximately 2.8 millimeters. 15. An interstitial x-ray needle, including: first means for producing a plurality of electrons, a tube disposed to receive the electrons from the first means and to pass the electrons through the tube, second means disposed at the end of the tube for receiving the electrons after the passage of the electrons through the tube and for converting the received electrons to x-rays, a casing disposed in enveloping relationship to the tube, there being a space between the tube and that casing, third means for passing a cooling fluid through the space between the tube and the casing and past the second means to cool the second means, and fourth means disposed in the space between the tube and the casing for confining the electrons to a beam during the passage of the electrons through the first tube to the second means. 16. An interstitial x-ray needle as set forth in claim 15, including, a housing enveloping the tube and the casing and the first means. 17. An interstitial x-ray tube as set forth in claim 16 wherein the casing has a diameter no greater than approximately 2.8 millimeters. 18. An interstitial x-ray tube as set forth in claim 15 wherein the tube has a tip and the second means includes a converter element disposed at the tip of the tube to receive the electrons after the passage of the electrons through the tube and to convert the received electrons to x-rays. 19. An interstitial x-ray tube as set forth in claim 15, including, at least one hollow pipe partially occupying the space between the tube and the casing to provide for the passage of the cooling fluid through the hollow pipe to the second means and to provide for the passage of the cooling fluid from the second means through the remaining space between the tube and the casing, the hollow pipe being included in the third means. 20. An interstitial x-ray tube as set forth in claim 15 wherein the fourth means is operative to confine the electron beam to a diameter no greater than approximately four tenths of a millimeter (0.4 mm). 21. An interstitial x-ray needle, including: first means for producing a plurality of electrons, a tube disposed to receive the electrons from the first means and to pass the electrons through the tube, second means for receiving the electrons after the passage of the electrons through the tube and for converting the electrons to x-rays, a casing disposed in spaced relationship to the tube, third means for passing a cooling fluid through the space between the tube and the casing and past the second means to cool the second means, and magnetic means disposed on the tube in the space between the tube and the casing for confining the electrons to a beam during the flow of the electrons through the tube. |
The present invention generally pertains to X-ray apparatus and is particularly 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 U.S. Pat. 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 defining 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 element so that the X-rays can be concentrated at the tumor and thereby minimize radiation damage to adjacent 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.
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 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.
The interstitial X-ray needle of the present invention may be of such small diameter that 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. An X-ray needle of such diameter may be inserted 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 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 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.
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 flow 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.
FIG. 1 is a diagram of an X-ray apparatus including a preferred embodiment of the interstitial X-ray needle of the present invention.
FIG. 2 is a sectional view of the needle of FIG. 1 taken along lines 2--2.
FIG. 3 is a diagram of a portion of the needle illustrating an alternative preferred embodiment of the flow-chamber defining means.
FIG. 4 is a sectional view of the needle of FIG. 3 taken along lines 4--4.
Referring to FIGS. 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 12 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 between 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, and 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.
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 magnetic 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 0.1 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 chamber 42 between the tip 36 of the tube 24 and a coolant outlet 44 in the casing 30.
For a needle 10 of the embodiment of FIGS. 1 and 2, including a ten-centimeter long tube 24 having an inside diameter of 0.64 millimeter and an outside 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 millimeters 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 FIGS. 3 and 4, in an alternative preferred embodiment, the needle 10A includes an elongated X-ray tube 24, a converter 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 least one inlet opening (not shown) in the casing 30; and the space 50 between the tube 24 and the casing 30 not occupied by the pipes 46 defines an output flow chamber between the tip 36 of the tube 24 and an outlet opening (not shown) in the casing 30.
For a needle 10A of the embodiment of FIGS. 3 and 4, including a ten-centimeter long tube 24 having an inside diameter of 0.64 millimeter and an outside 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 jets 52 of 0.15 millimeter directed at the tip 36 of the needle 10A, a water flow rate of 10 milliliters-per-minute is obtained at an inlet pressure of 50 pounds-per-square-inch, whereby for a 20 watt heat rate at the tip 36 of the needle 10A, the water temperature 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 flexibe 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 converter element 26 by operating with an electron emitter voltage of 200 kilovolts and a beam current of 0.07 milliamperes.
In addition to providing benefits incident to its size, the miniature interstitial X-ray needle of the present invention also may generate controlled hyperthermic temperatures for application to the treated tumor, which combined with the radiation treatment may provide a synergistic healing effect.
Smith, John R., Miller, Robert B., Muehlenweg, Carl A.
Patent | Priority | Assignee | Title |
6661876, | Jul 30 2001 | Moxtek, Inc | Mobile miniature X-ray source |
7035379, | Sep 13 2002 | Moxtek, Inc | Radiation window and method of manufacture |
7158612, | Feb 21 2003 | NUCLETRON OPERATIONS B V | Anode assembly for an x-ray tube |
7233647, | Sep 13 2002 | Moxtek, Inc. | Radiation window and method of manufacture |
7382862, | Sep 30 2005 | Moxtek, Inc. | X-ray tube cathode with reduced unintended electrical field emission |
7428298, | Mar 31 2005 | Moxtek, Inc | Magnetic head for X-ray source |
7529345, | Jul 18 2007 | Moxtek, Inc. | Cathode header optic for x-ray tube |
7737424, | Jun 01 2007 | Moxtek, Inc | X-ray window with grid structure |
7756251, | Sep 28 2007 | Brigham Young University | X-ray radiation window with carbon nanotube frame |
7965818, | Jul 01 2008 | Minnesota Medical Physics LLC | Field emission X-ray apparatus, methods, and systems |
7983394, | Dec 17 2009 | Moxtek, Inc | Multiple wavelength X-ray source |
8005191, | Jul 01 2008 | Minnesota Medical Physics LLC | Field emission X-ray apparatus, methods, and systems |
8247971, | Mar 19 2009 | Moxtek, Inc | Resistively heated small planar filament |
8498381, | Oct 07 2010 | Moxtek, Inc | Polymer layer on X-ray window |
8526574, | Sep 24 2010 | Moxtek, Inc | Capacitor AC power coupling across high DC voltage differential |
8736138, | Sep 28 2007 | Brigham Young University | Carbon nanotube MEMS assembly |
8750458, | Feb 17 2011 | Moxtek, Inc | Cold electron number amplifier |
8761344, | Dec 29 2011 | Moxtek, Inc | Small x-ray tube with electron beam control optics |
8792619, | Mar 30 2011 | Moxtek, Inc | X-ray tube with semiconductor coating |
8804910, | Jan 24 2011 | Moxtek, Inc | Reduced power consumption X-ray source |
8817950, | Dec 22 2011 | Moxtek, Inc | X-ray tube to power supply connector |
8929515, | Feb 23 2011 | Moxtek, Inc | Multiple-size support for X-ray window |
8948345, | Sep 24 2010 | Moxtek, Inc | X-ray tube high voltage sensing resistor |
8964943, | Oct 07 2010 | Moxtek, Inc. | Polymer layer on X-ray window |
8989354, | May 16 2011 | Moxtek, Inc | Carbon composite support structure |
8995621, | Sep 24 2010 | Moxtek, Inc | Compact X-ray source |
9072154, | Dec 21 2012 | Moxtek, Inc | Grid voltage generation for x-ray tube |
9076628, | May 16 2011 | Moxtek, Inc | Variable radius taper x-ray window support structure |
9159525, | Jun 01 2011 | Canon Kabushiki Kaisha | Radiation generating tube |
9173623, | Apr 19 2013 | Moxtek, Inc | X-ray tube and receiver inside mouth |
9174412, | May 16 2011 | Brigham Young University | High strength carbon fiber composite wafers for microfabrication |
9177755, | Mar 04 2013 | Moxtek, Inc. | Multi-target X-ray tube with stationary electron beam position |
9184020, | Mar 04 2013 | Moxtek, Inc. | Tiltable or deflectable anode x-ray tube |
9305735, | Sep 28 2007 | Moxtek, Inc | Reinforced polymer x-ray window |
9351387, | Dec 21 2012 | Moxtek, Inc. | Grid voltage generation for x-ray tube |
Patent | Priority | Assignee | Title |
2356645, | |||
2362816, | |||
2651727, | |||
2748293, | |||
3609432, | |||
3668454, | |||
3783251, | |||
3969629, | Mar 14 1975 | Varian Associates | X-ray treatment machine having means for reducing secondary electron skin dose |
4157475, | Oct 21 1977 | Applied Radiation Corporation | Electron accelerator comprising a target exposed to the electron beam |
4409993, | Jul 23 1980 | Olympus Optical Co., Ltd. | Endoscope apparatus |
4763671, | Dec 27 1983 | Stanford University | Method of treating tumors using selective application of heat and radiation |
4825880, | Jun 19 1987 | The Regents of the University of California | Implantable helical coil microwave antenna |
4969863, | Oct 28 1988 | NUCLETRON B V | Adaptor for remote after-loading apparatus for radiotherapy |
4993430, | Jan 06 1987 | Omron Tateisi Electronics Co. | Electrode device for high frequency thermotherapy apparatus |
5026959, | Nov 16 1988 | TOKYO KEIKI CO , LTD | Microwave radiator for warming therapy |
Date | Maintenance Fee Events |
May 15 2000 | M184: Payment of Maintenance Fee, 8th Year, Large Entity. |
Aug 10 2004 | M1553: Payment of Maintenance Fee, 12th Year, Large Entity. |
Aug 10 2004 | M1556: 11.5 yr surcharge- late pmt w/in 6 mo, Large Entity. |
Date | Maintenance Schedule |
Nov 26 1999 | 4 years fee payment window open |
May 26 2000 | 6 months grace period start (w surcharge) |
Nov 26 2000 | patent expiry (for year 4) |
Nov 26 2002 | 2 years to revive unintentionally abandoned end. (for year 4) |
Nov 26 2003 | 8 years fee payment window open |
May 26 2004 | 6 months grace period start (w surcharge) |
Nov 26 2004 | patent expiry (for year 8) |
Nov 26 2006 | 2 years to revive unintentionally abandoned end. (for year 8) |
Nov 26 2007 | 12 years fee payment window open |
May 26 2008 | 6 months grace period start (w surcharge) |
Nov 26 2008 | patent expiry (for year 12) |
Nov 26 2010 | 2 years to revive unintentionally abandoned end. (for year 12) |