US3868522A - Superconducting cyclotron - Google Patents

Superconducting cyclotron Download PDF

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Publication number
US3868522A
US3868522A US419034A US41903473A US3868522A US 3868522 A US3868522 A US 3868522A US 419034 A US419034 A US 419034A US 41903473 A US41903473 A US 41903473A US 3868522 A US3868522 A US 3868522A
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pairs
plates
magnetic field
ions
region
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Clifford B Bigham
Harvey R Schneider
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Atomic Energy of Canada Ltd AECL
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Atomic Energy of Canada Ltd AECL
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    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H13/00—Magnetic resonance accelerators; Cyclotrons
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S505/00—Superconductor technology: apparatus, material, process
    • Y10S505/825—Apparatus per se, device per se, or process of making or operating same
    • Y10S505/879—Magnet or electromagnet

Definitions

  • This invention relates to an isochronous cyclotron and more particularly to a cyclotron for producing beams of heavy or light ions in which the magnetic field for orbiting the ions is produced by superconducting coils.
  • a cyclotron using an air core superconducting magnet system to provide high intensity magnetic fields.
  • iron sectors with spiral edges acting as flutter poles positioned in the magnetic field such that saturation of the iron in the sectors gives an increased field between the sectors and a slightly decreased field outside.
  • FIG. 1 is a cross-section of a cyclotron structure with superconducting coils
  • FIG. 2 is a plan view of the sectors
  • FIGS. 3A, 3B, 3C illustrate modes of operation of the rf accelerating structure.
  • FIG. 4 is a schematic of the proposed cyclotron and a tandem accelerator supply
  • FIG. 5 is a schematic of an injection system
  • FIG. 6 is a graphical representation of the magnetic field.
  • a superconducting cyclotron is contained in a vacuum tight enclosure 10 containing cryostat tanks 11 and 12 which contain superconducting main coils 13a, 13b, and 14a, 14b. Because of the large magnetic attraction between them, the large coils 13a and 13b require a fairly strong separating structure 15 positioned between them.
  • the design of these coils which is well within the scope of present superconducting magnet technology provides a magnetic field about three times that of an iron core structure of comparable size. This results in a much smaller overall size and reductions in space and containment requirement.
  • the accelerating structure is made up of eight upper and .lower conducting sectors (shown in plan view in FIG. 2) and shown in cross-section as 16a, 16b.
  • the hot sectors are connected alternately to quarter wave resonators 17a, 17b containing movable tuning shorts 18a, 18b. Energy is provided via a coaxial line 19a having a center conductor 20a which is connected to the tuning shorts.
  • the RF power supply (not shown) is generally conventional and in a typical design would provide 60 kw at 22-45 MHz.
  • the four upper and lower grounded sectors 160 (see FIG. 2) contain iron flutter pole pieces shown in cross section as 21a and 21b in FIG. 1.
  • B(R) is the average midplane field at radius R 'y(R) is the relativistic factor related to the ion kinetic energy T and rest energy E, by,
  • a magnetic field with a maximum azimuthally average value of 5T(50,000 G) and a shape matching B(R) to within i 0.1% is generated by the superconducting coils.
  • Normal trim coils 22a, 22b provide the necessary adjustment for isochronism.
  • the cyclotron is connected to an input ion beam source at 22 and provision is made at 23 for extraction of the accelerated beam.
  • the input beam is introduced tangentially and on the midplane to orbit inwardly to strike stripper foil 23 suitably mounted on a moveable carriage (not shown) for positioning purposes.
  • the ion energy and charge state on injection are chosen so that the most probable charge state after stripping is approximately four times the initial charge state.
  • the source accelerator tandem Van de Graaf generator
  • ions from Li to U can be injected into the cyclotron.
  • the ions orbit outwardly (approximately turns) from an inner orbit R,- to an outer orbit R being accelerated in the eight accelerating gaps 24 between the sector pairs.
  • the beam is extracted by electrostatic deflectors 25 positioned at the orbit periphery.
  • the four flutter pole sector pairs 21 are conveniently mounted in the grounded sectors 16c and are completely encased in conducting metal to shield the magnetic material (iron) from the RF.
  • the sectors have spiral edges 26 as shown to obtain sufficient focussing.
  • the device described in FIGS. 1 and 2 has two resonances and can be used in two modes, i.e., a 0-mode where the upper and lower resonator plates or sectors in each pair (A and B) are in phase and a ir-mode when the upper and lower plates are out of phase or in pushpull.
  • a 0-mode where the upper and lower resonator plates or sectors in each pair (A and B) are in phase
  • a ir-mode when the upper and lower plates are out of phase or in pushpull.
  • the ion velocity at extraction is twice that in the 0-mode as seen from FIGS. 38 and 3C.
  • the accelerating voltage at the gaps is Vm/ V2 compared to V,,, for the 0-mode because of the operation mode and therefore about twice the RF power is required.
  • FIG. 4 shows a typical arrangement with the cyclotron 30 being supplied from a negative ion source 31, a double drift harmonic buncher 32 for bunching the DC beam to a narrow phase width and a tandem accelerator 33 (with gas or foil stripper 34) for preaccelerating the beam.
  • An analyzing magnet 35 directs the ion beam with desired charge state to the foil stripper 23 in the cyclotron.
  • the output of the cyclotron is a heavy ion beam up to IOMeV/A or a light ion beam up to SOMeV/A.
  • FIG. 5 shows the mid-plane injection geometry in more detail. Stripper foil 23 has to be correctly positioned for each particular type of ion used.
  • Radial focussing of the beam results from the radially increasing field required for isochronism while vertical (or axial) focussing is achieved with an azimuthally varying field.
  • the latter is produced by the iron sectors (flutter poles) mounted above and below the midplane.
  • the radial and axial frequencies expressed as fractions of the cyclotron frequency are measures of the focussing forces, and are given by the following approximate relations k (N /N l') 1+2 tan e) k is the average field index,
  • N is the number of sectors
  • F is the flutter factor
  • F B B l and e is the flutter pole spiral angle.
  • the iron flutter poles will except for small edge effects, be uniformly magnetized with a magnetization equal to the saturation value M (M E (2/477) X Ampere turns/m for iron.)
  • the magnetic field of the magnetized iron poles 21a, 21b is superimposd on the coil field H, resulting in an increased field AH between the poles and a slightly decreased field outside.
  • the magnitude of the increase depends on the gap d between the poles. In the limit of a very small gap the field increase is equal to M
  • F ranges from 0015 at B 5Tto 0.06 at B 37.
  • Axial focussing should be adequate if 11 0.1, with a pole shape similar to that shown in FIG. 2, this is the case for ion energies up to 10 MeV/A at B ST and up to 50 MeV/A at B 3T.
  • a typical design for the main superconducting magnet would be as follows.
  • the superconducting coils are constructed of 76 pancake windings each with 130 turns of 1,000 A conductor.
  • the superconducting NbTi is in the form of fine filaments embedded in copper and twisted for stabilization against eddy currents. Sufficient copper conductor and cooling surface is allowed for complete cryostatic stabilization. This means that the coil could recover from any possible thermal transient.
  • a stainless steel ribbon is wound in with the conductor to keep the hoop stress below the yield point. The axial force is substantial so that a strong support is required between the coils.
  • the field in the coil is well below the critical value for NbTi.
  • the current density is in the range that has been used in some existing large magnets.
  • Extraction of the beam is achieved by initial deflections with electrostatic deflectors in adjacent grounded sectors. These deflections bring the beam out over the edge of the magnetic field where the orbit radius increases and the beam spirals out. Other extraction methods are possible.
  • An isochronous cyclotron for heavy or light ions comprising:
  • d. means for injecting the ions to be accelerated into an inner position in the orbital region
  • f. means for varying the magnetic field in the radial direction to provide radial focussing of the orbiting ion beam.
  • An isochronous cyclotron for heavy or light ions comprising:
  • pairs of sectoral conducting plates alternate pair of which are'at low or ground potential and the other pairs are connected to an RF voltage supply, defining an annular orbital region between the plates in the pairs and ion accelerating gaps between the edges of the pairs of plates and positioned in and generally orthogonal to the magnetic field in the central air core region, wherein the pairs of sectoral plates at ground or low voltage have associated and mounted adjacent to them pairs of shaped ferrous material structures, said pairs of structures being positioned in the magnetic field and as opposing pairs on each side of the orbital region such as to become saturated in the magnetic field and increase the magnetic field between them and thus providing a flutter pole axial focussing effect to the orbiting ions,
  • d. means for injecting the ions to be accelerated into an inner position in the orbital region
  • f. means for varying the magnetic field in the radial direction to provide radial focussing of the orbiting ion beam.
  • An isochronous cyclotron for heavy or light ions comprising:
  • d. means for injecting the ions to be accelerated into an inner position in the orbital region
  • trim coils mounted above and below the beam orbiting region to adjust the magnetic field shape in the air core region and provide an accurately isochronous radial profile
  • An isochronous cyclotron for heavy or light ions comprising:
  • a second pair of superconducting coils of smaller cross-section and diameter mounted radially inward of the first pair, said first and second pairs of coils capable of producing a strong unidirectional magnetic field in the air core region centrally of the coils,
  • means for injecting the ions to be accelerated into an inner position in the orbital region said means including a stripper foil for changing the charge state on incoming ions
  • means for extracting accelerated ions at an orbit location adjacent the periphery of the orbital region said means including capacitor plates carrying a potential such as to deflect the ion beam outwardly from the orbit region,
  • trim coils mounted above and below the beam space to adjust the magnetic field in the radial sense to provide an accurately isochronous radial field variation
  • each of said structures being positioned adjacent to each plate of the remaining alternate pairs of said sectoral plates, said plates being connected to ground or low potential
  • each of said structures being enclosed in conducting material to shield them from RF effects and having at least one spiral shaped edge, said spiral shape being predetermined for optimum axial focussing.

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  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Plasma & Fusion (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Particle Accelerators (AREA)
US419034A 1973-06-19 1973-11-26 Superconducting cyclotron Expired - Lifetime US3868522A (en)

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CA (1) CA966893A (de)
DE (1) DE2410994C2 (de)
FR (1) FR2234733B1 (de)
GB (1) GB1429463A (de)

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US4112306A (en) * 1976-12-06 1978-09-05 Varian Associates, Inc. Neutron irradiation therapy machine
WO1986007229A1 (en) * 1985-05-21 1986-12-04 Oxford Instruments Limited Improvements in cyclotrons
US4641104A (en) * 1984-04-26 1987-02-03 Board Of Trustees Operating Michigan State University Superconducting medical cyclotron
US4641057A (en) * 1985-01-23 1987-02-03 Board Of Trustees Operating Michigan State University Superconducting synchrocyclotron
EP0276123A2 (de) * 1987-01-22 1988-07-27 Oxford Instruments Limited Anordnung zur Erzeugung eines magnetischen Feldes
US4843333A (en) * 1987-01-28 1989-06-27 Siemens Aktiengesellschaft Synchrotron radiation source having adjustable fixed curved coil windings
US5017882A (en) * 1988-09-01 1991-05-21 Amersham International Plc Proton source
WO2004049770A1 (fr) 2002-11-25 2004-06-10 Ion Beam Applications S.A. Cyclotron ameliore
US20070171015A1 (en) * 2006-01-19 2007-07-26 Massachusetts Institute Of Technology High-Field Superconducting Synchrocyclotron
US20080093567A1 (en) * 2005-11-18 2008-04-24 Kenneth Gall Charged particle radiation therapy
US20090096179A1 (en) * 2007-10-11 2009-04-16 Still River Systems Inc. Applying a particle beam to a patient
US20090140671A1 (en) * 2007-11-30 2009-06-04 O'neal Iii Charles D Matching a resonant frequency of a resonant cavity to a frequency of an input voltage
US20090140672A1 (en) * 2007-11-30 2009-06-04 Kenneth Gall Interrupted Particle Source
US7656258B1 (en) 2006-01-19 2010-02-02 Massachusetts Institute Of Technology Magnet structure for particle acceleration
US20100045213A1 (en) * 2004-07-21 2010-02-25 Still River Systems, Inc. Programmable Radio Frequency Waveform Generator for a Synchrocyclotron
JP2011258427A (ja) * 2010-06-09 2011-12-22 Waseda Univ 空芯型サイクロトロン
US8558485B2 (en) 2011-07-07 2013-10-15 Ionetix Corporation Compact, cold, superconducting isochronous cyclotron
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
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
CN105103662A (zh) * 2012-09-28 2015-11-25 梅维昂医疗***股份有限公司 磁场再生器
US20160049228A1 (en) * 2014-07-28 2016-02-18 Bruker Biospin Ag Method for energizing a superconducting magnet arrangement
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
US20170069415A1 (en) * 2014-03-13 2017-03-09 Forschungszentrum Juelich Gmbh Superconducting magnetic field stabilizer
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
CN107371317A (zh) * 2016-05-13 2017-11-21 离子束应用股份有限公司 回旋加速器的***丘扇块设计
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
US20180192506A1 (en) * 2017-01-05 2018-07-05 Varian Medical Systems Particle Therapy Gmbh Cyclotron rf resonator tuning with asymmetrical fixed tuner
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
WO2019104878A1 (zh) * 2017-11-30 2019-06-06 合肥中科离子医学技术装备有限公司 一种回旋加速器中利用一次谐波调节粒子轨道对中的方法
US10375815B2 (en) 2017-11-30 2019-08-06 Hefei Cas Ion Medical And Technical Devices Co., Ltd. Method for adjusting particle orbit alignment by using first harmonic in cyclotron
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
CN114430607A (zh) * 2022-01-21 2022-05-03 中国原子能科学研究院 一种提高回旋加速器中心区聚焦力的螺旋型磁极结构
CN115460758A (zh) * 2022-11-08 2022-12-09 合肥中科离子医学技术装备有限公司 辐射防护屏蔽装置和使用其的回旋加速器
CN116170933A (zh) * 2023-01-09 2023-05-26 中国科学院近代物理研究所 用于应用型等时性回旋加速器的磁场装置

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JPH0782919B2 (ja) * 1985-06-10 1995-09-06 日本電信電話株式会社 電子加速器の励磁方法
JPS62136800A (ja) * 1985-12-07 1987-06-19 住友電気工業株式会社 Ｘ線発生装置
EP1069809A1 (de) * 1999-07-13 2001-01-17 Ion Beam Applications S.A. Isochrones Zyklotron und Verfahren zum Entfernen von geladenen Teilchen aus diesem Zyklotron
BE1019557A3 (fr) * 2010-10-27 2012-08-07 Ion Beam Applic Sa Synchrocyclotron.
JP5708984B2 (ja) * 2010-11-10 2015-04-30 学校法人早稲田大学 空芯型サイクロトロン
EP3244709B1 (de) * 2016-05-13 2020-01-01 Ion Beam Applications S.A. Gradientenkorrektor für zyklotron
US9907153B2 (en) 2016-05-13 2018-02-27 Ion Beam Applications S.A. Compact cyclotron
JP2020095774A (ja) * 2017-03-28 2020-06-18 住友重機械工業株式会社 空芯型サイクロトロン

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Cited By (96)

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Publication number Priority date Publication date Assignee Title
US4112306A (en) * 1976-12-06 1978-09-05 Varian Associates, Inc. Neutron irradiation therapy machine
US4641104A (en) * 1984-04-26 1987-02-03 Board Of Trustees Operating Michigan State University Superconducting medical cyclotron
US4641057A (en) * 1985-01-23 1987-02-03 Board Of Trustees Operating Michigan State University Superconducting synchrocyclotron
US4943781A (en) * 1985-05-21 1990-07-24 Oxford Instruments, Ltd. Cyclotron with yokeless superconducting magnet
WO1986007229A1 (en) * 1985-05-21 1986-12-04 Oxford Instruments Limited Improvements in cyclotrons
EP0276123A3 (en) * 1987-01-22 1989-07-26 Oxford Instruments Limited Magnetic field generating assembly
EP0276123A2 (de) * 1987-01-22 1988-07-27 Oxford Instruments Limited Anordnung zur Erzeugung eines magnetischen Feldes
US4843333A (en) * 1987-01-28 1989-06-27 Siemens Aktiengesellschaft Synchrotron radiation source having adjustable fixed curved coil windings
US5017882A (en) * 1988-09-01 1991-05-21 Amersham International Plc Proton source
WO2004049770A1 (fr) 2002-11-25 2004-06-10 Ion Beam Applications S.A. Cyclotron ameliore
US20060255285A1 (en) * 2002-11-25 2006-11-16 Ion Beam Applications S.A. Cyclotron
US7446490B2 (en) 2002-11-25 2008-11-04 Ion Beam Appliances S.A. Cyclotron
USRE48047E1 (en) 2004-07-21 2020-06-09 Mevion Medical Systems, Inc. Programmable radio frequency waveform generator for a synchrocyclotron
US20100045213A1 (en) * 2004-07-21 2010-02-25 Still River Systems, Inc. Programmable Radio Frequency Waveform Generator for a Synchrocyclotron
US8952634B2 (en) 2004-07-21 2015-02-10 Mevion Medical Systems, Inc. Programmable radio frequency waveform generator for a synchrocyclotron
US9925395B2 (en) 2005-11-18 2018-03-27 Mevion Medical Systems, Inc. Inner gantry
US10279199B2 (en) 2005-11-18 2019-05-07 Mevion Medical Systems, Inc. Inner gantry
US20080093567A1 (en) * 2005-11-18 2008-04-24 Kenneth Gall Charged particle radiation therapy
US10722735B2 (en) 2005-11-18 2020-07-28 Mevion Medical Systems, Inc. Inner gantry
US8916843B2 (en) 2005-11-18 2014-12-23 Mevion Medical Systems, Inc. Inner gantry
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US8907311B2 (en) 2005-11-18 2014-12-09 Mevion Medical Systems, Inc. Charged particle radiation therapy
US8344340B2 (en) 2005-11-18 2013-01-01 Mevion Medical Systems, Inc. Inner gantry
US7728311B2 (en) 2005-11-18 2010-06-01 Still River Systems Incorporated Charged particle radiation therapy
US9452301B2 (en) 2005-11-18 2016-09-27 Mevion Medical Systems, Inc. Inner gantry
US7696847B2 (en) * 2006-01-19 2010-04-13 Massachusetts Institute Of Technology High-field synchrocyclotron
US8614612B2 (en) * 2006-01-19 2013-12-24 Massachusetts Institute Of Technology Superconducting coil
US7920040B2 (en) 2006-01-19 2011-04-05 Massachusetts Institute Of Technology Niobium-tin superconducting coil
US20110193666A1 (en) * 2006-01-19 2011-08-11 Massachusetts Institute Of Technology Niobium-Tin Superconducting Coil
US20070171015A1 (en) * 2006-01-19 2007-07-26 Massachusetts Institute Of Technology High-Field Superconducting Synchrocyclotron
WO2007084701A1 (en) * 2006-01-19 2007-07-26 Massachusetts Institute Of Technology Magnet structure for particle acceleration
US8111125B2 (en) 2006-01-19 2012-02-07 Massachusetts Institute Of Technology Niobium-tin superconducting coil
US20120142538A1 (en) * 2006-01-19 2012-06-07 Massachusetts Institute Of Technology Superconducting Coil
US7656258B1 (en) 2006-01-19 2010-02-02 Massachusetts Institute Of Technology Magnet structure for particle acceleration
US7541905B2 (en) * 2006-01-19 2009-06-02 Massachusetts Institute Of Technology High-field superconducting synchrocyclotron
JP2009524200A (ja) * 2006-01-19 2009-06-25 マサチューセッツ・インスティテュート・オブ・テクノロジー 粒子加速のための磁石構造体
US20100148895A1 (en) * 2006-01-19 2010-06-17 Massachusetts Institute Of Technology Niobium-Tin Superconducting Coil
US20090206967A1 (en) * 2006-01-19 2009-08-20 Massachusetts Institute Of Technology High-Field Synchrocyclotron
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
US8003964B2 (en) 2007-10-11 2011-08-23 Still River Systems Incorporated Applying a particle beam to a patient
USRE48317E1 (en) 2007-11-30 2020-11-17 Mevion Medical Systems, Inc. Interrupted particle source
US8581523B2 (en) 2007-11-30 2013-11-12 Mevion Medical Systems, Inc. Interrupted particle source
US20090140672A1 (en) * 2007-11-30 2009-06-04 Kenneth Gall Interrupted Particle Source
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
US20090140671A1 (en) * 2007-11-30 2009-06-04 O'neal Iii Charles D Matching a resonant frequency of a resonant cavity to a frequency of an input voltage
US8970137B2 (en) 2007-11-30 2015-03-03 Mevion Medical Systems, Inc. Interrupted particle source
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