US3886367A - Ion-beam mask for cancer patient therapy - Google Patents

Ion-beam mask for cancer patient therapy Download PDF

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US3886367A
US3886367A US434458A US43445874A US3886367A US 3886367 A US3886367 A US 3886367A US 434458 A US434458 A US 434458A US 43445874 A US43445874 A US 43445874A US 3886367 A US3886367 A US 3886367A
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apertures
ions
mask
radiation
shielding material
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US434458A
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Jr John G Castle
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/10—Application or adaptation of safety means
    • 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
    • G—PHYSICS
    • G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
    • G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
    • G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
    • G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
    • G21K1/025—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using multiple collimators, e.g. Bucky screens; other devices for eliminating undesired or dispersed radiation
    • G—PHYSICS
    • G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
    • G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
    • G21K5/00—Irradiation devices
    • G21K5/04—Irradiation devices with beam-forming means
    • 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
    • A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
    • A61N2005/1087—Ions; Protons
    • 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
    • A61N2005/1092—Details
    • A61N2005/1095—Elements inserted into the radiation path within the system, e.g. filters or wedges

Definitions

  • ABSTRACT An ion-beam mask has been provided for spatially dis- 65 2 653 tributing fast ions used to irradiate tumors so that the o region near the Bragg peak receives a uniform radia
  • This invention relates generally to radiotherapy and more specifically to a shielding mask for use in ionbeam radiotherapy which allows distributed irradiation of an embedded tumor while shielding a substantial portion of the surface volume tissue.
  • a treatment of choice for cancer patients having embedded tumors is irradiation of the tumors with a beam of fast ions such as by a beam of 65 MeV protons produced by the Oak Ridge Isochronous Cyclotron (ORIC).
  • a beam of fast ions such as by a beam of 65 MeV protons produced by the Oak Ridge Isochronous Cyclotron (ORIC).
  • ORIC Oak Ridge Isochronous Cyclotron
  • the dose to be delivered to a specified target tumor region is usually prescribed to be uniform throughout the target volume to well within '5 percent.
  • the desired uniformity of accumulated dose laterally across the target volume is readily attained, as indicated, for example, by R. S.
  • an object of this invention to provide an ion beam mask for mitigating surface tissue effects of radiotherapeutic treatment of embedded tumors which will permit a beam of fast ions, such as protons to penetrate to the tumor and deliver with the desired uniformity over the lateral extent of the target volume at each exposure any prescribed dose level but which will, at the same time, leave a reasonable fraction of skin area either unirradiated or with a dose level low enough to enable the skin and dermal regions to more readily recover from the deterimental effects produced by the heavy charged particles.
  • FIG. 1 is a schematic illustration of a radiotherapy system employing the ion-beam mask according to the present invention.
  • FIG. 2 is a planar view of the ion-beam mask shown in FIG. 1.
  • FIG. 1 shows a cross section of one example of the subject ion-beam mask positioned over tissue having a tumor embedded therein.
  • the mask is shown generally at 10.
  • a beam of fast ions such as protons from a source 8 in the range of from 50 to 200 MeV, enters from the direction of arrows l2.
  • Mask I0 is preferably made of carbon (graphitized and purified) and has an array of holes 14 drilled therethrough to permit passage of the ions to the surface of the skin 16 whereupon the ions proceed to the target tumor 18.
  • the masked portions of the surface of skin 16 will receive less of a dose of ionizing radiation with the mask in place than they would if no carbon shield were interposed between the patient and the beam.
  • the purpose, therefore, of breaking the beam into many discrete portions whereby a large area of skin and intervening tis sue are protected from ionizing radiation can be achieved by means of the subject design provided that the thickness of the mask 10 exceeds sufficiently the range of the ions in the mask material.
  • a carbon mask is preferred, other suitable masking materials, such as dense plastics, aluminum, and denser metals, may be used.
  • FIG. 2 is a planar view of the device showing that the device consists simply of a shield 10 of a material, such as carbon, having parallel holes 14 drilled therein for collimation of the beam which passes therethrough.
  • the stated object of this invention can be fulfilled by an appropriate choice of the diameter (d) of the holes through the mask and of the wall thickness (w) between the holes to attain sufficient overlap between beamlets passing through adjacent holes at the depth of the Bragg peak, approximately the ion range (R,,) in the patients tissue.
  • Optimal overlap between adjacent beamlets and thereby optimal lateral uniformity of dose will occur, for the example of each beamlet having a Gaussian spread whose effective dispersion is o at the target depth of interest, when the sum of d and w is made equal to 1.5 01,.
  • the lateral Gaussian spread of each beamlet may be seen from the expression for the beam intensity l(.r, v) at depth y being I(x,y) R(y) exp (-fi/o'fi) where x is the lateral coordinate (from beamlet center) at which I(x,y) is specified. It should be noted that reasonable uniformity may be attained with factors differing considerably from this ideal Gaussian value of 1.5v For large depths, y, the effective dispersion, 0,, is related to the hole diameter, d, and the dispersion of the Gaussian spread associated with each ions motion through the tissue, 0 by the expression from the work of A. Koehler and W. Preston of the Harvard Cyclotron,
  • o gives the Gaussian spread for each fast ions lateral position as it moves through toward the end of its range R. Measurements show 0,, to be 0.031 R for protons moving through water and 0.045 R for protons moving through aluminum. This 0' is large enough for ions reaching depths such as 20 cm to permit d and w to be optimized
  • the hole 14 illustrated in FIG. 2 can be arrayed in a variety of configuration but it has been found that the hexagonal pattern, as illustrated in FIG. 2, provides a close packed array for the best uniformity at target depth near R.
  • d and w may be determined from the above expressions, suppose the radiotherapist were to relax his requirement of lateral uniformity from F 1.5 (the ideal) to Fcloser to 2, say F 1.73. then the design above of a suitable carbon mask gives a thickness of at least 8 cm and a choice of hole diameter and corresponding wall thickness including the sets of d 0.037 cm for w 0.37 cm and d 0.76 cm for w 0.12 cm.
  • This design procedure makes the subject invention compatible with accurate location control, i.e., the beam can be accurately repositioned during a series of exposures to effectively spare a web of skin and still deliver a uniform dose to a deeply embedded tumor.
  • the subject development is shown to break a beam of fast ions given to cancer patients for therapeutic purposes into separate and discrete rays whereby the region near the Bragg peak (the end of the range of ions, in tissue, for example) has a lateral dose uniform to within a few percent and whereby the skin surface area and underlying tissues receive a discontinuous dosage of irradiation thereby enabling the skin to heal more readily than it would if exposed to a massive dose covering the entire area interposed between the radiation source and the tumor.
  • a radiation mask for mitigating the surface tissue effects of a radiotherapeutic treatment of embedded tumors in a patient by means of a beam of fast ions from a beam source comprising:
  • a block of radiation shielding material positioned in said beam intermediate the patient and said beam source, said block having a surface area larger than the cross section of said beam and a thickness greater than the range of ions of said beam in said shielding material, said shielding material block having a plurality of circular cross section apertures extending therethrough in a direction parallel to the rays of said beam and arranged in an orderly, evenly spaced array, each of said apertures having a diameter (d) and spaced with a wall thickness (w) therebetween defined by d w F0 with fbeing in the range of from 1 to 2 and where 0",, is the effective dispersion of the ions passing through said apertures at the depth of said embedded tumor to attain sufficient overlap of discrete beam portions passing through adjacent ones of said apertures at the depth of the Bragg peak for said beam source coincident with the tumor region, thereby providing a lateral uniformity of radiation dose over the irradiated area of said tumor while shielding a sub stantial are of skin and intervening tissue.

Abstract

An ion-beam mask has been provided for spatially distributing fast ions used to irradiate tumors so that the region near the Bragg peak receives a uniform radiation dose while the tissue at the point of entrance of the beam has a web of unirradiated volume to promote healing of the surface tissue following radiotherapeutic treatment of embedded tumors.

Description

United States Patent [191 H Castle, Jr.
[ 1 May 27, 1975 [5 ION-BEAM MASK FOR CANCER PATIENT 3,407,300 10/ 1968 Hansen 250/505 THERAPY 3,543.384 l2/l970 Hansen 250/505 3,7l0,l l9 1/1973 Eymery U 250/505 Inventor: John Castl Jr., Huntsvill Alav 3.777,]48 12/1973 Miraldi 2501505 [73] Assignee: The United States of America as represented by the United States Primary Examiner-Eli Lieberman Energy Research and Develo ment Assistant Examiner-D. C. Nelms Administration, Washington, DC. Attorney, Agent, or Firm.lohn A. Horan; David S. Filed: Jan. 1974 Zachry, David E. Breeden [Zl] Appl. No.: 434,458 {57] ABSTRACT An ion-beam mask has been provided for spatially dis- 65 2 653 tributing fast ions used to irradiate tumors so that the o region near the Bragg peak receives a uniform radia [58] Field of Search 250,494 67 2 tion dose while the tissue at the point of entrance of the beam has a web of unirradiated volume to promote healing of the surface tissue following radiother- [56] Reterences C'ted apeutic treatment of embedded tumors.
UNITED STATES PATENTS 2,133.385 10/1938 Freeman 2501505 3 Clams, 2 Drawmfl 8" l /18 ?Q /g ION BEAM SOURCE PATENTEDHM 27 m5 ION BEAM SOURCE 1 ION-BEAM MASK FOR CANCER PATIENT THERAPY The present invention was made during the course of, or under, a contract with the United States Atomic Energy Commission.
BACKGROUND OF THE INVENTION This invention relates generally to radiotherapy and more specifically to a shielding mask for use in ionbeam radiotherapy which allows distributed irradiation of an embedded tumor while shielding a substantial portion of the surface volume tissue.
A treatment of choice for cancer patients having embedded tumors is irradiation of the tumors with a beam of fast ions such as by a beam of 65 MeV protons produced by the Oak Ridge Isochronous Cyclotron (ORIC). Such a treatment frequently results in destruction of the malignant cells with a consequent remission of the cancer. The dose to be delivered to a specified target tumor region is usually prescribed to be uniform throughout the target volume to well within '5 percent. The desired uniformity of accumulated dose laterally across the target volume is readily attained, as indicated, for example, by R. S. Benders measurements on the proton beam at ORIC as reported in the Annual Progress Report of the Electronuclear Division of the Oak Ridge National Laboratory, Oak Ridge, Tenn, for I967, on pages l01l02, by using only the control portion of a wide beam of fast ions, masked to cover the lateral extent of the target volume. The desired uniformity longitudinally through the depth of the target volume is readily obtained by modifying the range of the ions for certain fractions of the total exposure time. Unfortunately, healthly tissues between the outer epidermis and the tumor itself must be exposed to the damaging fast protons as they seek out the target tumor.
SUMMARY OF THE INVENTION In view of the above, it is an object of this invention to provide an ion beam mask for mitigating surface tissue effects of radiotherapeutic treatment of embedded tumors which will permit a beam of fast ions, such as protons to penetrate to the tumor and deliver with the desired uniformity over the lateral extent of the target volume at each exposure any prescribed dose level but which will, at the same time, leave a reasonable fraction of skin area either unirradiated or with a dose level low enough to enable the skin and dermal regions to more readily recover from the deterimental effects produced by the heavy charged particles.
Other objects and many of the attendant advantages of the present invention will be obvious from the fol lowing detailed description taken in conjunction with the drawings.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a schematic illustration of a radiotherapy system employing the ion-beam mask according to the present invention.
FIG. 2 is a planar view of the ion-beam mask shown in FIG. 1.
DETAILED DESCRIPTION The subject invention is best illustrated by referring to the drawings. FIG. 1 shows a cross section of one example of the subject ion-beam mask positioned over tissue having a tumor embedded therein. The mask is shown generally at 10. A beam of fast ions, such as protons from a source 8 in the range of from 50 to 200 MeV, enters from the direction of arrows l2. Mask I0 is preferably made of carbon (graphitized and purified) and has an array of holes 14 drilled therethrough to permit passage of the ions to the surface of the skin 16 whereupon the ions proceed to the target tumor 18. The masked portions of the surface of skin 16 will receive less of a dose of ionizing radiation with the mask in place than they would if no carbon shield were interposed between the patient and the beam. The purpose, therefore, of breaking the beam into many discrete portions whereby a large area of skin and intervening tis sue are protected from ionizing radiation can be achieved by means of the subject design provided that the thickness of the mask 10 exceeds sufficiently the range of the ions in the mask material. Although a carbon mask is preferred, other suitable masking materials, such as dense plastics, aluminum, and denser metals, may be used.
FIG. 2 is a planar view of the device showing that the device consists simply of a shield 10 of a material, such as carbon, having parallel holes 14 drilled therein for collimation of the beam which passes therethrough.
The stated object of this invention can be fulfilled by an appropriate choice of the diameter (d) of the holes through the mask and of the wall thickness (w) between the holes to attain sufficient overlap between beamlets passing through adjacent holes at the depth of the Bragg peak, approximately the ion range (R,,) in the patients tissue. Optimal overlap between adjacent beamlets and thereby optimal lateral uniformity of dose will occur, for the example of each beamlet having a Gaussian spread whose effective dispersion is o at the target depth of interest, when the sum of d and w is made equal to 1.5 01,. The lateral Gaussian spread of each beamlet may be seen from the expression for the beam intensity l(.r, v) at depth y being I(x,y) R(y) exp (-fi/o'fi) where x is the lateral coordinate (from beamlet center) at which I(x,y) is specified. It should be noted that reasonable uniformity may be attained with factors differing considerably from this ideal Gaussian value of 1.5v For large depths, y, the effective dispersion, 0,, is related to the hole diameter, d, and the dispersion of the Gaussian spread associated with each ions motion through the tissue, 0 by the expression from the work of A. Koehler and W. Preston of the Harvard Cyclotron,
where o gives the Gaussian spread for each fast ions lateral position as it moves through toward the end of its range R. Measurements show 0,, to be 0.031 R for protons moving through water and 0.045 R for protons moving through aluminum. This 0' is large enough for ions reaching depths such as 20 cm to permit d and w to be optimized The hole 14 illustrated in FIG. 2 can be arrayed in a variety of configuration but it has been found that the hexagonal pattern, as illustrated in FIG. 2, provides a close packed array for the best uniformity at target depth near R.
Consider the illustration of planning to deliver a certain dose at depth R l2 cm. The proton beam energy needed is MeV for which each protons spread has 0-,, 0.03 IR 0.37 cm in soft tissue. For the optimal lateral uniformity, the sum d w is chosen equal to a factor F times the effective Gaussian dispersion of each beamlet at depth R to have the value of F 1.5 for Gaussian beams (d w F01). For round holes the optimum uniformity at the proton range R,, R is attainable by setting F I5 and specifying d/w by the expression acceptable uniformity may be attainabie with F values in the range of about l to 2. The variety of consistent values of d and w include one set of d 0.60 cm and w 0.12 cm and another set ofd=0. l8 cm hole diame ter and w 0.36 cm wall thickness.
To further illustrate the way in which d and w may be determined from the above expressions, suppose the radiotherapist were to relax his requirement of lateral uniformity from F 1.5 (the ideal) to Fcloser to 2, say F 1.73. then the design above of a suitable carbon mask gives a thickness of at least 8 cm and a choice of hole diameter and corresponding wall thickness including the sets of d 0.037 cm for w 0.37 cm and d 0.76 cm for w 0.12 cm.
This design procedure makes the subject invention compatible with accurate location control, i.e., the beam can be accurately repositioned during a series of exposures to effectively spare a web of skin and still deliver a uniform dose to a deeply embedded tumor.
In summary, the subject development is shown to break a beam of fast ions given to cancer patients for therapeutic purposes into separate and discrete rays whereby the region near the Bragg peak (the end of the range of ions, in tissue, for example) has a lateral dose uniform to within a few percent and whereby the skin surface area and underlying tissues receive a discontinuous dosage of irradiation thereby enabling the skin to heal more readily than it would if exposed to a massive dose covering the entire area interposed between the radiation source and the tumor.
What is claimed is:
l. A radiation mask for mitigating the surface tissue effects of a radiotherapeutic treatment of embedded tumors in a patient by means of a beam of fast ions from a beam source, comprising:
a block of radiation shielding material positioned in said beam intermediate the patient and said beam source, said block having a surface area larger than the cross section of said beam and a thickness greater than the range of ions of said beam in said shielding material, said shielding material block having a plurality of circular cross section apertures extending therethrough in a direction parallel to the rays of said beam and arranged in an orderly, evenly spaced array, each of said apertures having a diameter (d) and spaced with a wall thickness (w) therebetween defined by d w F0 with fbeing in the range of from 1 to 2 and where 0",, is the effective dispersion of the ions passing through said apertures at the depth of said embedded tumor to attain sufficient overlap of discrete beam portions passing through adjacent ones of said apertures at the depth of the Bragg peak for said beam source coincident with the tumor region, thereby providing a lateral uniformity of radiation dose over the irradiated area of said tumor while shielding a sub stantial are of skin and intervening tissue.
2. The radiation mask as set forth in claim 1 wherein said beam of fast ions is protons in the range of from S0 to 200 MeV and said shielding material is carbon.
3. The radiation mask as set forth in claim 2 wherein the apertures in said shield are arrayed in a hexagonal pattern.

Claims (3)

1. A radiation mask for mitigating the surface tissue effects of a radiotherapeutic treatment of embedded tumors in a patient by means of a beam of fast ions from a beam source, comprising: a block of radiation shielding material positioned in said beam intermediate the patient and said beam source, said block having a surface area larger than the cross section of said beam and a thickness greater than the range of ions of said beam in said shielding material, said shielding material block having a plurality of circular cross section apertures extending therethrough in a direction parallel to the rays of said beam and arranged in an orderly, evenly spaced array, each of said apertures having a diameter (d) and spaced with a wall thickness (w) therebetween defined by d w F sigma e, with f being in the range of from 1 to 2 and where sigma e is the effective dispersion of the ions passing through said apertures at the depth of said embedded tumor to attain sufficient overlap of discrete beam portions passing through adjacent ones of said apertures at the depth of the Bragg peak for said beam source coincident with the tumor region, thereby providing a lateral uniformity of radiation dose over the irradiated area of said tumor while shielding a substantial are of skin and intervening tissue.
2. The radiation mask as set forth in claim 1 wherein said beam of fast ions is protons in the range of from 50 to 200 MeV and said shielding material is carbon.
3. The radiation mask as set forth in claim 2 wherein the apertures in said shield are arrayed in a hexagonal pattern.
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US4194123A (en) * 1978-05-12 1980-03-18 Rockwell International Corporation Lithographic apparatus
US4532646A (en) * 1983-06-16 1985-07-30 The United States Of America As Represented By The Department Of Energy X-ray focal spot locating apparatus and method
US20090096179A1 (en) * 2007-10-11 2009-04-16 Still River Systems Inc. Applying a particle beam to a patient
US20090140672A1 (en) * 2007-11-30 2009-06-04 Kenneth Gall Interrupted Particle Source
US20100230617A1 (en) * 2005-11-18 2010-09-16 Still River Systems Incorporated, a Delaware Corporation Charged particle radiation therapy
US8791656B1 (en) 2013-05-31 2014-07-29 Mevion Medical Systems, Inc. Active return system
US8927950B2 (en) 2012-09-28 2015-01-06 Mevion Medical Systems, Inc. Focusing a particle beam
US8933650B2 (en) 2007-11-30 2015-01-13 Mevion Medical Systems, Inc. Matching a resonant frequency of a resonant cavity to a frequency of an input voltage
US8952634B2 (en) 2004-07-21 2015-02-10 Mevion Medical Systems, Inc. Programmable radio frequency waveform generator for a synchrocyclotron
US9155186B2 (en) 2012-09-28 2015-10-06 Mevion Medical Systems, Inc. Focusing a particle beam using magnetic field flutter
US9185789B2 (en) 2012-09-28 2015-11-10 Mevion Medical Systems, Inc. Magnetic shims to alter magnetic fields
US9301384B2 (en) 2012-09-28 2016-03-29 Mevion Medical Systems, Inc. Adjusting energy of a particle beam
US9545528B2 (en) 2012-09-28 2017-01-17 Mevion Medical Systems, Inc. Controlling particle therapy
US9622335B2 (en) 2012-09-28 2017-04-11 Mevion Medical Systems, Inc. Magnetic field regenerator
US9661736B2 (en) 2014-02-20 2017-05-23 Mevion Medical Systems, Inc. Scanning system for a particle therapy system
US9681531B2 (en) 2012-09-28 2017-06-13 Mevion Medical Systems, Inc. Control system for a particle accelerator
US9723705B2 (en) 2012-09-28 2017-08-01 Mevion Medical Systems, Inc. Controlling intensity of a particle beam
US9730308B2 (en) 2013-06-12 2017-08-08 Mevion Medical Systems, Inc. Particle accelerator that produces charged particles having variable energies
US9950194B2 (en) 2014-09-09 2018-04-24 Mevion Medical Systems, Inc. Patient positioning system
US9962560B2 (en) 2013-12-20 2018-05-08 Mevion Medical Systems, Inc. Collimator and energy degrader
US10254739B2 (en) 2012-09-28 2019-04-09 Mevion Medical Systems, Inc. Coil positioning system
US10258810B2 (en) 2013-09-27 2019-04-16 Mevion Medical Systems, Inc. Particle beam scanning
US10646728B2 (en) 2015-11-10 2020-05-12 Mevion Medical Systems, Inc. Adaptive aperture
US10653892B2 (en) 2017-06-30 2020-05-19 Mevion Medical Systems, Inc. Configurable collimator controlled using linear motors
US10675487B2 (en) 2013-12-20 2020-06-09 Mevion Medical Systems, Inc. Energy degrader enabling high-speed energy switching
US10925147B2 (en) 2016-07-08 2021-02-16 Mevion Medical Systems, Inc. Treatment planning
US11103730B2 (en) 2017-02-23 2021-08-31 Mevion Medical Systems, Inc. Automated treatment in particle therapy
US11291861B2 (en) 2019-03-08 2022-04-05 Mevion Medical Systems, Inc. Delivery of radiation by column and generating a treatment plan therefor

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US3543384A (en) * 1966-11-14 1970-12-01 Picker Corp Methods of collimator fabrication
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Cited By (52)

* Cited by examiner, † Cited by third party
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US4194123A (en) * 1978-05-12 1980-03-18 Rockwell International Corporation Lithographic apparatus
US4532646A (en) * 1983-06-16 1985-07-30 The United States Of America As Represented By The Department Of Energy X-ray focal spot locating apparatus and method
US8952634B2 (en) 2004-07-21 2015-02-10 Mevion Medical Systems, Inc. Programmable radio frequency waveform generator for a synchrocyclotron
USRE48047E1 (en) 2004-07-21 2020-06-09 Mevion Medical Systems, Inc. Programmable radio frequency waveform generator for a synchrocyclotron
US9452301B2 (en) 2005-11-18 2016-09-27 Mevion Medical Systems, Inc. Inner gantry
US9925395B2 (en) 2005-11-18 2018-03-27 Mevion Medical Systems, Inc. Inner gantry
US20100230617A1 (en) * 2005-11-18 2010-09-16 Still River Systems Incorporated, a Delaware Corporation Charged particle radiation therapy
US8344340B2 (en) 2005-11-18 2013-01-01 Mevion Medical Systems, Inc. Inner gantry
US10279199B2 (en) 2005-11-18 2019-05-07 Mevion Medical Systems, Inc. Inner gantry
US8907311B2 (en) 2005-11-18 2014-12-09 Mevion Medical Systems, Inc. Charged particle radiation therapy
US8916843B2 (en) 2005-11-18 2014-12-23 Mevion Medical Systems, Inc. Inner gantry
US10722735B2 (en) 2005-11-18 2020-07-28 Mevion Medical Systems, Inc. Inner gantry
US8003964B2 (en) 2007-10-11 2011-08-23 Still River Systems Incorporated Applying a particle beam to a patient
US8941083B2 (en) 2007-10-11 2015-01-27 Mevion Medical Systems, Inc. Applying a particle beam to a patient
US20090096179A1 (en) * 2007-10-11 2009-04-16 Still River Systems Inc. Applying a particle beam to a patient
US8933650B2 (en) 2007-11-30 2015-01-13 Mevion Medical Systems, Inc. Matching a resonant frequency of a resonant cavity to a frequency of an input voltage
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