A synchrocyclotron comprises a resonant circuit that includes electrodes having a gap therebetween across the magnetic field. An oscillating voltage input, having a variable amplitude and frequency determined by a programmable digital waveform generator generates an oscillating electric field across the gap. The synchrocyclotron can include a variable capacitor in circuit with the electrodes to vary the resonant frequency. The synchrocyclotron can further include an injection electrode and an extraction electrode having voltages controlled by the programmable digital waveform generator. The synchrocyclotron can further include a beam monitor. The synchrocyclotron can detect resonant conditions in the resonant circuit by measuring the voltage and or current in the resonant circuit, driven by the input voltage, and adjust the capacitance of the variable capacitor or the frequency of the input voltage to maintain the resonant conditions. The programmable waveform generator can adjust at least one of the oscillating voltage input, the voltage on the injection electrode and the voltage on the extraction electrode according to beam intensity and in response to changes in resonant conditions.
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1. A synchrocyclotron comprising:
a magnetic field generator;
a resonant circuit, comprising:
electrodes, disposed between magnetic poles, having a gap therebetween across a magnetic field; and
a variable reactive element in circuit with the electrodes to vary a resonant frequency of the resonant circuit; and
a voltage input generator to provide a voltage input to the resonant circuit, the voltage input being an oscillating voltage that varies in frequency over a time of acceleration of charged particles.
11. A method of accelerating particles in a synchrocyclotron, comprising:
providing particles in the synchrocyclotron;
providing a resonant circuit, the resonant circuit comprising accelerating electrodes having a gap therebetween across a magnetic field; and
with a voltage input generator, applying an oscillating voltage input that varies in frequency during acceleration of the particles to the resonant circuit, the oscillating voltage input creating an oscillating electric field across the gap that accelerates the particles in the synchrocyclotron.
3. The synchrocyclotron of
4. The synchrocyclotron of
5. The synchrocyclotron of
6. The synchrocyclotron of
7. The synchrocyclotron of
8. The synchrocyclotron of
9. The synchrocyclotron as claimed in
10. The synchrocyclotron of
13. The method of
14. The method of
15. The method of
16. The method of
17. The method of
19. The method as in
20. The method as in
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This application is a continuation of U.S. application Ser. No. 12/011,466, filed Jan. 25, 2008 now U.S. Pat. No. 7,626,347, which is a continuation of U.S. application Ser. No. 11/371,622, filed Mar. 9, 2006, now U.S. Pat. No. 7,402,963, which is a continuation of U.S. application Ser. No. 11/187,633, filed Jul. 21, 2005, now abandoned, which claims the benefit of U.S. Provisional Application No. 60/590,089, filed on Jul. 21, 2004.
The entire teachings of the above applications are incorporated herein by reference.
In order to accelerate charged particles to high energies, many types of particle accelerators have been developed since the 1930s. One type of particle accelerator is a cyclotron. A cyclotron accelerates charged particles in an axial magnetic field by applying an alternating voltage to one or more “dees” in a vacuum chamber. The name “dee” is descriptive of the shape of the electrodes in early cyclotrons, although they may not resemble the letter D in some cyclotrons. The spiral path produced by the accelerating particles is normal to the magnetic field. As the particles spiral out, an accelerating electric field is applied at the gap between the dees. The radio frequency (RF) voltage creates an alternating electric field across the gap between the dees. The RF voltage, and thus the field, is synchronized to the orbital period of the charged particles in the magnetic field so that the particles are accelerated by the radio frequency waveform as they repeatedly cross the gap. The energy of the particles increases to an energy level far in excess of the peak voltage of the applied radio frequency (RF) voltage. As the charged particles accelerate, their masses grow due to relativistic effects. Consequently, the acceleration of the particles becomes non-uniform and the particles arrive at the gap asynchronously with the peaks of the applied voltage.
Two types of cyclotrons presently employed, an isochronous cyclotron and a synchrocyclotron, overcome the challenge of increase in relativistic mass of the accelerated particles in different ways. The isochronous cyclotron uses a constant frequency of the voltage with a magnetic field that increases with radius to maintain proper acceleration. The synchrocyclotron uses a decreasing magnetic field with increasing radius and varies the frequency of the accelerating voltage to match the mass increase caused by the relativistic velocity of the charged particles.
In a synchrocyclotron, discrete “bunches” of charged particles are accelerated to the final energy before the cycle is started again. In isochronous cyclotrons, the charged particles can be accelerated continuously, rather than in bunches, allowing higher beam power to be achieved.
In a synchrocyclotron, capable of accelerating a proton, for example, to the energy of 250 MeV, the final velocity of protons is 0.61 c, where c is the speed of light, and the increase in mass is 27% above rest mass. The frequency has to decrease by a corresponding amount, in addition to reducing the frequency to account for the radially decreasing magnetic field strength. The frequency's dependence on time will not be linear, and an optimum profile of the function that describes this dependence will depend on a large number of details.
Accurate and reproducible control of the frequency over the range required by a desired final energy that compensates for both relativistic mass increase and the dependency of magnetic field on the distance from the center of the dee has historically been a challenge. Additionally, the amplitude of the accelerating voltage may need to be varied over the accelerating cycle to maintain focusing and increase beam stability. Furthermore, the dees and other hardware comprising a cyclotron define a resonant circuit, where the dees may be considered the electrodes of a capacitor. This resonant circuit is described by Q-factor, which contributes to the profile of voltage across the gap.
A synchrocyclotron for accelerating charged particles, such as protons, can comprise a magnetic field generator and a resonant circuit that comprising electrodes, disposed between magnetic poles. A gap between the electrodes can be disposed across the magnetic field. An oscillating voltage input drives an oscillating electric field across the gap. The oscillating voltage input can be controlled to vary over the time of acceleration of the charged particles. Either or both the amplitude and the frequency of the oscillating voltage input can be varied. The oscillating voltage input can be generated by a programmable digital waveform generator.
The resonant circuit can further include a variable reactive element in circuit with the voltage input and electrodes to vary the resonant frequency of the resonant circuit. The variable reactive element may be a variable capacitance element such as a rotating condenser or a vibrating reed. By varying the reactance of such a reactive element and adjusting the resonant frequency of the resonant circuit, the resonant conditions can be maintained over the operating frequency range of the synchrocyclotron.
The synchrocyclotron can further include a voltage sensor for measuring the oscillating electric field across the gap. By measuring the oscillating electric field across the gap and comparing it to the oscillating voltage input, resonant conditions in the resonant circuit can be detected. The programmable waveform generator can be adjusting the voltage and frequency input to maintain the resonant conditions.
The synchrocyclotron can further include an injection electrode, disposed between the magnetic poles, under a voltage controlled by the programmable digital waveform generator. The injection electrode is used for injecting charged particles into the synchrocyclotron. The synchrocyclotron can further including an extraction electrode, disposed between the magnetic poles, under a voltage controlled by the programmable digital waveform generator. The extraction electrode is used to extract a particle beam from the synchrocyclotron.
The synchrocyclotron can further include a beam monitor for measuring particle beam properties. For example, the beam monitor can measure particle beam intensity, particle beam timing or spatial distribution of the particle beam. The programmable waveform generator can adjust at least one of the voltage input, the voltage on the injection electrode and the voltage on the extraction electrode to compensate for variations in the particle beam properties.
This invention is intended to address the generation of the proper variable frequency and amplitude modulated signals for efficient injection into, acceleration by, and extraction of charged particles from an accelerator.
The foregoing and other objects, features and advantages of the invention will be apparent from the following more particular description of preferred embodiments of the invention, as illustrated in the accompanying drawings in which like reference characters refer to the same parts throughout the different views. The drawings are not necessarily to scale, emphasis instead being placed upon illustrating the principles of the invention.
This invention relates to the devices and methods for generating the complex, precisely timed accelerating voltages across the “dee” gap in a synchrocyclotron. This invention comprises an apparatus and a method for driving the voltage across the “dee” gap by generating a specific waveform, where the amplitude, frequency and phase is controlled in such a manner as to create the most effective particle acceleration given the physical configuration of the individual accelerator, the magnetic field profile, and other variables that may or may not be known a priori. A synchrocyclotron needs a decreasing magnetic field in order to maintain focusing of the particles beam, thereby modifying the desired shape of the frequency sweep. There are predictable finite propagation delays of the applied electrical signal to the effective point on the dee where the accelerating particle bunch experiences the electric field that leads to continuous acceleration. The amplifier used to amplify the radio frequency (RF) signal that drives the voltage across the dee gap may also have a phase shift that varies with frequency. Some of the effects may not be known a priori, and may be only observed after integration of the entire synchrocyclotron. In addition, the timing of the particle injection and extraction on a nanosecond time scale can increase the extraction efficiency of the accelerator, thus reducing stray radiation due to particles lost in the accelerating and extraction phases of operation.
Referring to
The accelerating electrodes comprise “dee” 10 and “dee” 12, having gap 13 therebetween. Dee 10 is connected to an alternating voltage potential whose frequency is changed from high to low during the accelerating cycle in order to account for the increasing relativistic mass of a charged particle and radially decreasing magnetic field (measured from the center of vacuum chamber 8) produced by coils 2a and 2b and pole portions 4a and 4b. The characteristic profile of the alternating voltage in dees 10 and 12 is show in
Ion source 18 that includes ion source electrode 20, located at the center of vacuum chamber 8, is provided for injecting charged particles. Extraction electrodes 22 are provided to direct the charge particles into extraction channel 24, thereby forming beam 26 of the charged particles. The ion source may also be mounted externally and inject the ions substantially axially into the acceleration region.
Dees 10 and 12 and other pieces of hardware that comprise a cyclotron, define a tunable resonant circuit under an oscillating voltage input that creates an oscillating electric field across gap 13. This resonant circuit can be tuned to keep the Q-factor high during the frequency sweep by using a tuning means.
As used herein, Q-factor is a measure of the “quality” of a resonant system in its response to frequencies close to the resonant frequency. Q-factor is defined as
Q=1/R×√(L/C),
where R is the active resistance of a resonant circuit, L is the inductance and C is the capacitance of this circuit.
Tuning means can be either a variable inductance coil or a variable capacitance. A variable capacitance device can be a vibrating reed or a rotating condenser. In the example shown in
The blade rotation can be synchronized with the RF frequency generation so that by varying the Q-factor of the RF cavity, the resonant frequency of the resonant circuit, defined by the cyclotron, is kept close to the frequency of the alternating voltage potential applied to “dees” 10 and 12.
The rotation of the blades can be controlled by the digital waveform generator, described below with reference to
A sensor that detects the peak resonant condition (not shown) can also be employed to provide feedback to the clock of the digital waveform generator to maintain the highest match to the resonant frequency. The sensors for detecting resonant conditions can measure the oscillating voltage and current in the resonant circuit. In another example, the sensor can be a capacitance sensor. This method can accommodate small irregularities in the relationship between the profile of the meshing blades of the rotating condenser and the angular position of the shaft.
A vacuum pumping system 40 maintains vacuum chamber 8 at a very low pressure so as not to scatter the accelerating beam.
To achieve uniform acceleration in a synchrocyclotron, the frequency and the amplitude of the electric field across the “dee” gap needs to be varied to account for the relativistic mass increase and radial (measured as distance from the center of the spiral trajectory of the charged particles) variation of magnetic field as well as to maintain focus of the beam of particles.
The instant invention uses a set of high speed digital to analog converters (DAC) that can generate, from a high speed memory, the required signals on a nanosecond time scale. Referring to
Referring to
Synchrocyclotron 300 includes digital waveform generator 319. Digital waveform generator 319 comprises one or more digital-to-analog converters (DACs) 320 that convert digital representations of waveforms stored in memory 322 into analog signals. Controller 324 controls addressing of memory 322 to output the appropriate data and controls DACs 320 to which the data is applied at any point in time. Controller 324 also writes data to memory 322. Interface 326 provides a data link to an outside computer (not shown). Interface 326 can be a fiber optic interface.
The clock signal that controls the timing of the “analog-to-digital” conversion process can be made available as an input to the digital waveform generator. This signal can be used in conjunction with a shaft position encoder (not shown) on the rotating condenser (see
The signal generated by DAC 320c is passed on to amplifying system 330, operated under the control of RF amplifier control system 332. In amplifying system 330, the signal from DAC 320c is applied by RF driver 334 to RF splitter 336, which sends the RF signal to be amplified by an RF power amplifier 338. In the example shown in
Upon exit from amplifying system 330, the signal from DAC 320c is passed on to particle accelerator 302 through matching network 348. Matching network 348 matches impedance of a load (particle accelerator 302) and a source (amplifying system 330). Matching network 348 includes a set of variable reactive elements.
Synchrocyclotron 300 can further include optimizer 350. Using measurement of the intensity of beam 318 by beam monitor 316, optimizer 350, under the control of a programmable processor can adjust the waveforms produced by DACs 320a, b and c and their timing to optimize the operation of the synchrocyclotron 300 and achieve a optimum acceleration of the charged particles.
The principles of operation of digital waveform generator 319 and adaptive feedback system 350 will now be discussed with reference to
The initial conditions for the waveforms can be calculated from physical principles that govern the motion of charged particles in magnetic field, from relativistic mechanics that describe the behavior of a charged particle mass as well as from the theoretical description of magnetic field as a function of radius in a vacuum chamber. These calculations are performed at step 402. The theoretical waveform of the voltage at the dee gap, RF(ω, t), where ω is the frequency of the electrical field across the dee gap and t is time, is computed based on the physical principles of a cyclotron, relativistic mechanics of a charged particle motion, and theoretical radial dependency of the magnetic field.
Departures of practice from theory can be measured and the waveform can be corrected as the synchrocyclotron operates under these initial conditions. For example, as will be described below with reference to
The timing of the accelerator waveform can be adjusted and optimized, as described below, on a cycle-by-cycle basis to correct for propagation delays present in the physical arrangement of the radio frequency wiring; asymmetry in the placement or manufacture of the dees can be corrected by placing the peak positive voltage closer in time to the subsequent peak negative voltage or vice versa, in effect creating an asymmetric sine wave.
In general, waveform distortion due to characteristics of the hardware can be corrected by pre-distorting the theoretical waveform RF(ω, t) using a device-dependent transfer function A, thus resulting in the desired waveform appearing at the specific point on the acceleration electrode where the protons are in the acceleration cycle. Accordingly, and referring again to
At step 405, a waveform that corresponds to an expression RF(ω, t)/A(ω,t) is computed and stored in memory 322. At step 406, digital waveform generator 319 generates RF /A waveform from memory. The driving signal RF(ω, t)/A(ω, t) is amplified at step 408, and the amplified signal is propagated through the entire device 300 at step 410 to generate a voltage across the dee gap at step 412. A more detailed description of a representative transfer function A(ω,t) will be given below with reference to
After the beam has reached the desired energy, a precisely timed voltage can be applied to an extraction electrode or device to create the desired beam trajectory in order to extract the beam from the accelerator, where it is measured by beam monitor at step 414a. RF voltage and frequency is measured by voltage sensors at step 414b. The information about beam intensity and RF frequency is relayed back to digital waveform generator 319, which can now adjust the shape of the signal RF(ω, t)/A(ω, t) at step 406.
The entire process can be controlled at step 416 by optimizer 350. Optimizer 350 can execute a semi- or fully automatic algorithm designed to optimize the waveforms and the relative timing of the waveforms. Simulated annealing is an example of a class of optimization algorithms that may be employed. On-line diagnostic instruments can probe the beam at different stages of acceleration to provide feedback for the optimization algorithm. When the optimum conditions have been found, the memory holding the optimized waveforms can be fixed and backed up for continued stable operation for some period of time. This ability to adjust the exact waveform to the properties of the individual accelerator decreases the unit-to-unit variability in operation and can compensate for manufacturing tolerances and variation in the properties of the materials used in the construction of the cyclotron.
The concept of the rotating condenser (such as condenser 28 shown in
The structure of rotating condenser 28 (see
As mentioned above, the timing of the waveform of the oscillating voltage input can be adjusted to correct for propagation delays that arise in the device.
In
As described above, the digital waveform generator produces an oscillating input voltage of the form RF(ω, t)/A(ω, t), where RF(ω, t) is a desired voltage across the dee gap and A(ω, t) is a transfer function. A representative device-specific transfer function A, is illustrated by curve 600 in
Another example of the type of effects that can be controlled with the programmable waveform generator is shown in
With the use of the programmable waveform generator, the amplitude of accelerating voltage 708 can be modulated in the desired fashion, as shown in
As mentioned above, the programmable waveform generator can be used to control the ion injector (ion source) to achieve optimal acceleration of the charged particles by precisely timing particle injections.
While this invention has been particularly shown and described with references to preferred embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the invention encompassed by the appended claims.
Patent | Priority | Assignee | Title |
Patent | Priority | Assignee | Title |
2280606, | |||
2492324, | |||
2615129, | |||
2616042, | |||
2659000, | |||
2701304, | |||
2789222, | |||
3175131, | |||
3432721, | |||
3582650, | |||
3679899, | |||
3689847, | |||
3757118, | |||
3868522, | |||
3886367, | |||
3925676, | |||
3955089, | Oct 21 1974 | Varian Associates | Automatic steering of a high velocity beam of charged particles |
3958327, | May 01 1974 | Airco, Inc. | Stabilized high-field superconductor |
3992625, | Dec 27 1973 | Jersey Nuclear-Avco Isotopes, Inc. | Method and apparatus for extracting ions from a partially ionized plasma using a magnetic field gradient |
4038622, | Apr 13 1976 | The United States of America as represented by the United States Energy | Superconducting dipole electromagnet |
4047068, | Nov 26 1973 | Kreidl Chemico Physical K.G. | Synchronous plasma packet accelerator |
4112306, | Dec 06 1976 | Varian Associates, Inc. | Neutron irradiation therapy machine |
4129784, | Jan 16 1973 | Siemens Medical Systems, Inc | Gamma camera |
4139777, | Nov 19 1975 | Cyclotron and neutron therapy installation incorporating such a cyclotron | |
4197510, | Jun 23 1978 | The United States of America as represented by the Secretary of the Navy | Isochronous cyclotron |
4220866, | Dec 30 1977 | Siemens Aktiengesellschaft | Electron applicator |
4230129, | Jan 24 1974 | THERMAL DEVELOPMENTS, INC | Radio frequency, electromagnetic radiation device having orbital mount |
4256966, | Jul 03 1979 | Siemens Medical Laboratories, Inc. | Radiotherapy apparatus with two light beam localizers |
4336505, | Jul 14 1980 | GIGA-TRONICS, INCORPORATED | Controlled frequency signal source apparatus including a feedback path for the reduction of phase noise |
4345210, | May 31 1979 | C.G.R. MeV | Microwave resonant system with dual resonant frequency and a cyclotron fitted with such a system |
4353033, | Mar 07 1979 | Rikagaku Kenkyusho | Magnetic pole structure of an isochronous-cyclotron |
4425506, | Nov 19 1981 | VARIAN ASSOCIATES, INC , A CORP OF DE | Stepped gap achromatic bending magnet |
4490616, | Sep 30 1982 | Cephalometric shield | |
4507614, | Mar 21 1983 | The United States of America as represented by the United States | Electrostatic wire for stabilizing a charged particle beam |
4507616, | Mar 08 1982 | Board of Trustees Operating Michigan State University | Rotatable superconducting cyclotron adapted for medical use |
4589126, | Jan 26 1984 | Radiotherapy treatment table | |
4598208, | Oct 04 1982 | Varian Associates, Inc. | Collimation system for electron arc therapy |
4628523, | May 13 1985 | B V OPTISCHE INDUSTRIE DE OUDE DELFT | Direction control for radiographic therapy apparatus |
4633125, | May 09 1985 | BOARD OF TRUSTEES, EAST LANSING, MI A CONSTITUTIONAL CORPORATION OF MI | Vented 360 degree rotatable vessel for containing liquids |
4641057, | Jan 23 1985 | Board of Trustees | Superconducting synchrocyclotron |
4641104, | Apr 26 1984 | BOARD OF TRUSTEES, EAST LANSING, MICHIGAN, A CONSTITUTIONAL CORPORATION OPERATING MICHIGAN | Superconducting medical cyclotron |
4651007, | Sep 13 1984 | Technicare Corporation | Medical diagnostic mechanical positioner |
4680565, | Jun 24 1985 | Siemens Aktiengesellschaft | Magnetic field device for a system for the acceleration and/or storage of electrically charged particles |
4705955, | Apr 02 1985 | Scanditronix AB | Radiation therapy for cancer patients |
4710722, | Mar 08 1985 | Siemens Aktiengesellschaft | Apparatus generating a magnetic field for a particle accelerator |
4726046, | Nov 05 1985 | VARIAN MEDICAL SYSTEMS TECHNOLOGIES, INC | X-ray and electron radiotherapy clinical treatment machine |
4734653, | Feb 25 1985 | Siemens Aktiengesellschaft | Magnetic field apparatus for a particle accelerator having a supplemental winding with a hollow groove structure |
4737727, | Feb 12 1986 | Mitsubishi Denki Kabushiki Kaisha | Charged beam apparatus |
4739173, | Apr 11 1986 | Board of Trustees Operating Michigan State University | Collimator apparatus and method |
4745367, | Mar 28 1985 | Kernforschungszentrum Karlsruhe GmbH; Brown, Boveri & Cie AG | Superconducting magnet system for particle accelerators of a synchrotron radiation source |
4754147, | Apr 11 1986 | Michigan State University | Variable radiation collimator |
4769623, | Jan 28 1987 | Siemens Aktiengesellschaft | Magnetic device with curved superconducting coil windings |
4771208, | May 10 1985 | UNIVERSITE CATHOLIQUE DE LOUVAIN, HALLES UNIVERSITAIRES, PLACE DE 1 UNIVERSITE 1, B-1348 LOUVAIN-LA-NEUVE, BELGIUM | Cyclotron |
4783634, | Feb 27 1986 | Mitsubishi Denki Kabushiki Kaisha | Superconducting synchrotron orbital radiation apparatus |
4808941, | Oct 29 1986 | Siemens Aktiengesellschaft | Synchrotron with radiation absorber |
4812658, | Jul 23 1987 | President and Fellows of Harvard College | Beam Redirecting |
4843333, | Jan 28 1987 | Siemens Aktiengesellschaft | Synchrotron radiation source having adjustable fixed curved coil windings |
4865284, | Mar 13 1984 | Siemens Gammasonics, Inc. | Collimator storage device in particular a collimator cart |
4868843, | Sep 10 1986 | VARIAN MEDICAL SYSTEMS TECHNOLOGIES, INC | Multileaf collimator and compensator for radiotherapy machines |
4868844, | Sep 10 1986 | VARIAN MEDICAL SYSTEMS TECHNOLOGIES, INC | Mutileaf collimator for radiotherapy machines |
4870287, | Mar 03 1988 | Loma Linda University Medical Center | Multi-station proton beam therapy system |
4880985, | Oct 05 1988 | Detached collimator apparatus for radiation therapy | |
4902993, | Feb 19 1987 | Kernforschungszentrum Karlsruhe GmbH | Magnetic deflection system for charged particles |
4904949, | Aug 28 1984 | OXFORD INSTRUMENTS LIMITED, OSNEY MEAD, OXFORD OX2 ODX UNITED KINGDOM | Synchrotron with superconducting coils and arrangement thereof |
4905267, | Apr 29 1988 | Loma Linda University Medical Center | Method of assembly and whole body, patient positioning and repositioning support for use in radiation beam therapy systems |
4917344, | Apr 07 1988 | Loma Linda University Medical Center | Roller-supported, modular, isocentric gantry and method of assembly |
4943781, | May 21 1985 | Oxford Instruments, Ltd.; Amersham International plc | Cyclotron with yokeless superconducting magnet |
4987309, | Nov 29 1988 | VARIAN INTERNATIONAL AG | Radiation therapy unit |
4996496, | Sep 11 1987 | Hitachi, LTD; Nippon Telegraph and Telephone Corporation | Bending magnet |
5017789, | Mar 31 1989 | Loma Linda University Medical Center | Raster scan control system for a charged-particle beam |
5017882, | Sep 01 1988 | AMERSHAM INTERNATIONAL PLC, AMERSHAM PLACE, LITTLE CHALFONT, BUCKINGHAMSHIRE HP7 9NA, ENGLAND; OXFORD INSTRUMENTS LIMITED, OSNEY MEAD, OXFORD, OX2 ODX, ENGLAND | Proton source |
5036290, | Mar 15 1989 | Hitachi, Ltd.; Nippon Telegraph and Telephone Corp. | Synchrotron radiation generation apparatus |
5039057, | Apr 07 1988 | Loma Linda University Medical Center | Roller-supported, modular, isocentric gentry and method of assembly |
5039867, | Aug 24 1987 | Mitsubishi Denki Kabushiki Kaisha | Therapeutic apparatus |
5072123, | May 03 1990 | VARIAN ASSOCIATES, INC , A CORP OF DE | Method of measuring total ionization current in a segmented ionization chamber |
5111173, | Mar 27 1990 | Mitsubishi Denki Kabushiki Kaisha | Deflection electromagnet for a charged particle device |
5117194, | Aug 26 1988 | Mitsubishi Denki Kabushiki Kaisha | Device for accelerating and storing charged particles |
5117212, | Jan 12 1989 | Mitsubishi Denki Kabushiki Kaisha | Electromagnet for charged-particle apparatus |
5117829, | Mar 31 1989 | Loma Linda University Medical Center; LOMA LINDA UNIVERSITY MEDICAL CENTER, LOMA LINDA, CA 92350 | Patient alignment system and procedure for radiation treatment |
5148032, | Jun 28 1991 | Siemens Medical Solutions USA, Inc | Radiation emitting device with moveable aperture plate |
5166531, | Aug 05 1991 | Varian Medical Systems, Inc | Leaf-end configuration for multileaf collimator |
5189687, | Dec 02 1988 | University of Florida Research Foundation, Incorporated | Apparatus for stereotactic radiosurgery |
5240218, | Oct 23 1991 | Loma Linda University Medical Center | Retractable support assembly |
5260581, | Mar 04 1992 | Loma Linda University Medical Center | Method of treatment room selection verification in a radiation beam therapy system |
5278533, | Aug 31 1990 | Mitsubishi Denki Kabushiki Kaisha | Coil for use in charged particle deflecting electromagnet and method of manufacturing the same |
5317164, | Jun 12 1991 | Mitsubishi Denki Kabushiki Kaisha | Radiotherapy device |
5336891, | Jun 16 1992 | Arch Development Corporation | Aberration free lens system for electron microscope |
5341104, | Feb 05 1993 | Siemens Aktiengesellschaft | Synchrotron radiation source |
5349198, | Jul 15 1992 | Mitsubishi Denki Kabushiki Kaisha | Beam supply device |
5365742, | Jan 25 1991 | Saes Getters S.p.A. | Device and process for the removal of hydrogen from a vacuum enclosure at cryogenic temperatures and especially high energy particle accelerators |
5374913, | Dec 13 1991 | Houston Advanced Research Center | Twin-bore flux pipe dipole magnet |
5382914, | May 05 1992 | ACCSYS TECHNOLOGY, INC | Proton-beam therapy linac |
5401973, | Dec 04 1992 | IOTRON INDUSTRIES CANADA INC | Industrial material processing electron linear accelerator |
5405235, | Jul 26 1991 | Barrel grasping device for automatically clamping onto the pole of a barrel trolley | |
5434420, | Dec 04 1992 | IOTRON INDUSTRIES CANADA INC | Industrial material processing electron linear accelerator |
5440133, | Jul 02 1993 | Loma Linda University Medical Center | Charged particle beam scattering system |
5451794, | Dec 04 1992 | IOTRON INDUSTRIES CANADA INC | Electron beam current measuring device |
5461773, | Aug 31 1990 | Mitsubishi Denki Kabushiki Kaisha | Method of manufacturing coils for use in charged particle deflecting electromagnet |
5463291, | Dec 23 1993 | SIEMENS MEDICAL SOLUTIONS, USA, INC | Cyclotron and associated magnet coil and coil fabricating process |
5492922, | Feb 28 1995 | Eli Lilly and Company | Benzothiophene compounds intermediate compositions and methods for inhibiting aortal smooth muscle proliferation |
5511549, | Feb 13 1995 | Loma Linda University Medical Center | Normalizing and calibrating therapeutic radiation delivery systems |
5521469, | Nov 22 1991 | ION BEAM APPLICATIONS S A | Compact isochronal cyclotron |
5561697, | Dec 15 1992 | Hitachi Medical | Microtron electron accelerator |
5585642, | Feb 15 1995 | Loma Linda University Medical Center | Beamline control and security system for a radiation treatment facility |
5635721, | Sep 19 1994 | HITESYS S P A | Apparatus for the liner acceleration of electrons, particularly for intraoperative radiation therapy |
5668371, | Jun 06 1995 | Wisconsin Alumni Research Foundation | Method and apparatus for proton therapy |
5691679, | Oct 27 1994 | General Electric Company | Ceramic superconducting lead resistant to moisture and breakage |
5726448, | Aug 09 1996 | ZIMMER, INC | Rotating field mass and velocity analyzer |
5751781, | Oct 07 1995 | ELE KKTA AB | Apparatus for treating a patient |
5778047, | Oct 24 1996 | Varian Medical Systems, Inc | Radiotherapy couch top |
5783914, | Mar 17 1994 | Hitachi, Ltd. | Particle beam accelerator, and a method of operation |
5811944, | Jun 25 1996 | Lawrence Livermore National Security LLC | Enhanced dielectric-wall linear accelerator |
5818058, | Jan 18 1996 | Mitsubishi Denki Kabushiki Kaisha | Particle beam irradiation apparatus |
5821705, | Jun 25 1996 | Lawrence Livermore National Security LLC | Dielectric-wall linear accelerator with a high voltage fast rise time switch that includes a pair of electrodes between which are laminated alternating layers of isolated conductors and insulators |
5825845, | Oct 28 1996 | Loma Linda University Medical Center | Proton beam digital imaging system |
5841237, | Jul 14 1997 | Lockheed Martin Energy Research Corporation | Production of large resonant plasma volumes in microwave electron cyclotron resonance ion sources |
5846043, | Aug 05 1997 | Cart and caddie system for storing and delivering water bottles | |
5851182, | Sep 11 1996 | Megavoltage radiation therapy machine combined to diagnostic imaging devices for cost efficient conventional and 3D conformal radiation therapy with on-line Isodose port and diagnostic radiology | |
5866912, | Apr 18 1995 | Loma Linda University Medical Center | System and method for multiple particle therapy |
5874811, | Aug 19 1994 | GE Healthcare Limited | Superconducting cyclotron for use in the production of heavy isotopes |
5895926, | Feb 15 1995 | Loma Linda University Medical Center | Beamline control and security system for a radiation treatment facility |
5920601, | Oct 25 1996 | Battelle Energy Alliance, LLC | System and method for delivery of neutron beams for medical therapy |
5929458, | May 07 1996 | Hitachi, Ltd.; Hitachi Engineering Services Co., Ltd. | Radiation shield |
5993373, | Aug 08 1997 | Sumitomo Heavy Industries, Ltd. | Rotating radiation chamber for radiation therapy |
6034377, | Nov 12 1997 | Mitsubishi Denki Kabushiki Kaisha | Charged particle beam irradiation apparatus and method of irradiation with charged particle beam |
6057655, | Oct 06 1995 | Ion Beam Applications, S.A. | Method for sweeping charged particles out of an isochronous cyclotron, and device therefor |
6061426, | Oct 06 1997 | U S PHILIPS CORPORATION | X-ray examination apparatus including an x-ray filter |
6094760, | Aug 04 1997 | Sumitomo Heavy Industries, LTD; OBAYASHI MANUFACTURING CO , LTD | Bed system for radiation therapy |
6241671, | Nov 03 1998 | STEREOTAXIS, INC | Open field system for magnetic surgery |
6265837, | Mar 10 1998 | Hitachi, Ltd. | Charged-particle beam irradiation method and system |
6268610, | Oct 20 1997 | Mitsubishi Denki Kabushiki Kaisha | Charged-particle beam irradiation apparatus, charged-particle beam rotary irradiation system, and charged-particle beam irradiation method |
6278239, | Jun 25 1996 | Lawrence Livermore National Security LLC | Vacuum-surface flashover switch with cantilever conductors |
6279579, | Oct 23 1998 | Varian Medical Systems, Inc | Method and system for positioning patients for medical treatment procedures |
6316776, | Aug 30 1996 | Hitachi, LTD | Charged particle beam apparatus and method for operating the same |
6407505, | Feb 01 2001 | Siemens Medical Solutions USA, Inc | Variable energy linear accelerator |
6417634, | Sep 29 1998 | Gems Pet Systems AB | Device for RF control |
6433336, | Dec 21 1998 | Ion Beam Applications S.A. | Device for varying the energy of a particle beam extracted from an accelerator |
6433349, | Mar 10 1998 | Hitachi, Ltd. | Charged-particle beam irradiation method and system |
6433494, | Apr 22 1999 | Inductional undulative EH-accelerator | |
6441569, | Dec 09 1998 | Particle accelerator for inducing contained particle collisions | |
6443349, | Jul 22 1999 | Device and method for inserting an information carrier | |
6476403, | Apr 01 1999 | Gesellschaft fuer Schwerionenforschung mbH | Gantry with an ion-optical system |
6492922, | Dec 14 2000 | Xilinx Inc. | Anti-aliasing filter with automatic cutoff frequency adaptation |
6501981, | Mar 16 1999 | MIDCAP FUNDING IV TRUST, AS SUCCESSOR TO EXISTING ADMINISTRATIVE AGENT | Apparatus and method for compensating for respiratory and patient motions during treatment |
6519316, | Nov 02 2001 | Siemens Medical Solutions USA, Inc.. | Integrated control of portal imaging device |
6600164, | Feb 19 1999 | Gesellschaft fuer Schwerionenforschung mbH | Method of operating an ion beam therapy system with monitoring of beam position |
6621889, | Oct 23 1998 | Varian Medical Systems, Inc | Method and system for predictive physiological gating of radiation therapy |
6639234, | Feb 19 1999 | Gesellschaft fuer Schwerionenforschung mbH | Method for checking beam steering in an ion beam therapy system |
6646383, | Mar 15 2001 | Siemens Medical Solutions USA, Inc. | Monolithic structure with asymmetric coupling |
6670618, | Feb 19 1999 | Gesellschaft fuer Schwerionenforschung mbH | Method of checking an isocentre and a patient-positioning device of an ion beam therapy system |
6683318, | Sep 11 1998 | Gesellschaft fuer Schwerionenforschung mbH | Ion beam therapy system and a method for operating the system |
6683426, | Jul 13 1999 | Ion Beam Applications S.A. | Isochronous cyclotron and method of extraction of charged particles from such cyclotron |
6693283, | Feb 06 2001 | Gesellschaft fuer Schwerionenforschung mbH | Beam scanning system for a heavy ion gantry |
6710362, | Jul 02 2001 | Gesellschaft fuer Schwerionenforschung mbH | Device for irradiating a tumor tissue |
6717162, | Dec 24 1998 | Ion Beam Applications S.A. | Method for treating a target volume with a particle beam and device implementing same |
6736831, | Feb 19 1999 | Gesellschaft fuer Schwerionenforschung mbH | Method for operating an ion beam therapy system by monitoring the distribution of the radiation dose |
6745072, | Feb 19 1999 | Gesellschaft fuer Schwerionenforschung mbH | Method for checking beam generation and beam acceleration means of an ion beam therapy system |
6769806, | Oct 30 2001 | Loma Linda University Medical Center | Method and device for delivering radiotherapy |
6774383, | Mar 26 2002 | Hitachi, Ltd. | Particle therapy system |
6777689, | Nov 16 2001 | Ion Beam Application, S.A. | Article irradiation system shielding |
6777700, | Jun 12 2002 | Hitachi, Ltd. | Particle beam irradiation system and method of adjusting irradiation apparatus |
6799068, | Feb 19 1999 | Gesellschaft fuer Schwerionenforschung mbH | Method for verifying the calculated radiation dose of an ion beam therapy system |
6800866, | Sep 11 2001 | Hitachi, Ltd. | Accelerator system and medical accelerator facility |
6803591, | Sep 30 2002 | Hitachi, Ltd.; Hitachi Setsubi Engineering Co., Ltd. | Medical particle irradiation apparatus |
6814694, | Jun 25 1999 | PAUL SCHERRER INSTITUT | Device for carrying out proton therapy |
6853703, | Jul 20 2001 | Siemens Medical Solutions USA, Inc | Automated delivery of treatment fields |
6864770, | Jan 30 2003 | Hitachi, Ltd. | Super conductive magnet apparatus |
6865254, | Jul 02 2002 | C-Rad Innovation AB | Radiation system with inner and outer gantry parts |
6891177, | Feb 19 1999 | Gesellschaft fuer Schwerionenforschung mbH | Ion beam scanner system and operating method |
6897451, | Sep 05 2002 | MAN Technologie AG; Gesellschaft fuer Schwerionenforschung mit beschraenkter Haftung | Isokinetic gantry arrangement for the isocentric guidance of a particle beam and a method for constructing same |
6914396, | Jul 31 2000 | L-3 Communications Corporation | Multi-stage cavity cyclotron resonance accelerator |
6953943, | Feb 28 2002 | Hitachi, Ltd. | Medical charged particle irradiation apparatus |
6969194, | Jun 09 1999 | C-Rad Innovation AB | Stable rotatable radiation gantry |
6984835, | Apr 23 2003 | Mitsubishi Denki Kabushiki Kaisha | Irradiation apparatus and irradiation method |
6993112, | Mar 12 2002 | Deutsches Krebsforschungszentrum Stiftung Des Offentlichen Rechts | Device for performing and verifying a therapeutic treatment and corresponding computer program and control method |
7008105, | May 13 2002 | Siemens Healthcare GmbH | Patient support device for radiation therapy |
7014361, | May 11 2005 | Adaptive rotator for gantry | |
7026636, | Jun 12 2002 | Hitachi, Ltd. | Particle beam irradiation system and method of adjusting irradiation apparatus |
7038403, | Jul 31 2003 | GE MEDICAL TECHNOLOGY SERVICES, INC | Method and apparatus for maintaining alignment of a cyclotron dee |
7060997, | Mar 26 2002 | Hitachi, Ltd. | Particle therapy system |
7122966, | Dec 16 2004 | General Electric Company | Ion source apparatus and method |
7122978, | Apr 19 2004 | Mitsubishi Denki Kabushiki Kaisha | Charged-particle beam accelerator, particle beam radiation therapy system using the charged-particle beam accelerator, and method of operating the particle beam radiation therapy system |
7173385, | Jan 15 2004 | Lawrence Livermore National Security LLC | Compact accelerator |
7208748, | Jul 21 2004 | LIFE SCIENCES ALTERNATIVE FUNDING LLC | Programmable particle scatterer for radiation therapy beam formation |
7262565, | Jul 21 2004 | National Institute of Radiological Sciences | Spiral orbit charged particle accelerator and its acceleration method |
7318805, | Mar 16 1999 | MIDCAP FUNDING IV TRUST, AS SUCCESSOR TO EXISTING ADMINISTRATIVE AGENT | Apparatus and method for compensating for respiratory and patient motion during treatment |
7348579, | Sep 18 2002 | PAUL SCHERRER INSTITUT | Arrangement for performing proton therapy |
7355189, | Sep 10 2003 | Hitachi, Ltd. | Charged particle therapy system, range modulation wheel device, and method of installing range modulation wheel device |
7402963, | Jul 21 2004 | LIFE SCIENCES ALTERNATIVE FUNDING LLC | Programmable radio frequency waveform generator for a synchrocyclotron |
7449701, | Apr 14 2003 | Hitachi, Ltd. | Particle beam irradiation equipment and particle beam irradiation method |
7466085, | Apr 17 2007 | BEST ABT, INC | Cyclotron having permanent magnets |
7476883, | May 26 2006 | BEST ABT, INC | Biomarker generator system |
7541905, | Jan 19 2006 | LIFE SCIENCES ALTERNATIVE FUNDING LLC | High-field superconducting synchrocyclotron |
7656258, | Jan 19 2006 | LIFE SCIENCES ALTERNATIVE FUNDING LLC | Magnet structure for particle acceleration |
7696847, | Jan 19 2006 | LIFE SCIENCES ALTERNATIVE FUNDING LLC | High-field synchrocyclotron |
7728311, | Nov 18 2005 | LIFE SCIENCES ALTERNATIVE FUNDING LLC | Charged particle radiation therapy |
7801269, | Jul 28 2006 | Accuray Incorporated | Method and apparatus for calibrating a radiation therapy treatment system |
8003964, | Oct 11 2007 | LIFE SCIENCES ALTERNATIVE FUNDING LLC | Applying a particle beam to a patient |
20020172317, | |||
20030048080, | |||
20030125622, | |||
20030136924, | |||
20030152197, | |||
20030163015, | |||
20030183779, | |||
20030234369, | |||
20040000650, | |||
20040017888, | |||
20040056212, | |||
20040061077, | |||
20040061078, | |||
20040085023, | |||
20040098445, | |||
20040111134, | |||
20040118081, | |||
20040149934, | |||
20040159795, | |||
20040173763, | |||
20040174958, | |||
20040183033, | |||
20040183035, | |||
20040200982, | |||
20040200983, | |||
20040213381, | |||
20040227104, | |||
20040232356, | |||
20040240626, | |||
20050058245, | |||
20050089141, | |||
20050161618, | |||
20050184686, | |||
20050228255, | |||
20050234327, | |||
20050247890, | |||
20060017015, | |||
20060067468, | |||
20060126792, | |||
20060145088, | |||
20060284562, | |||
20070001128, | |||
20070013273, | |||
20070014654, | |||
20070023699, | |||
20070029510, | |||
20070051904, | |||
20070092812, | |||
20070145916, | |||
20070171015, | |||
20070181519, | |||
20070284548, | |||
20080093567, | |||
20080218102, | |||
20090096179, | |||
20090140671, | |||
20090140672, | |||
20090200483, | |||
20100045213, | |||
CA2629333, | |||
CN101061759, | |||
CN101932361, | |||
CN101933405, | |||
CN101933406, | |||
CN1537657, | |||
DE2753397, | |||
DE3148100, | |||
DE3530446, | |||
DE4101094, | |||
DE4411171, | |||
EP194728, | |||
EP208163, | |||
EP221987, | |||
EP222786, | |||
EP277521, | |||
EP306966, | |||
EP388123, | |||
EP465597, | |||
EP499253, | |||
EP776595, | |||
EP864337, | |||
EP911064, | |||
EP1069809, | |||
EP1153398, | |||
EP1294445, | |||
EP1348465, | |||
EP1358908, | |||
EP1371390, | |||
EP1402923, | |||
EP1430932, | |||
EP1454653, | |||
EP1454654, | |||
EP1454655, | |||
EP1454656, | |||
EP1454657, | |||
EP1477206, | |||
EP1605742, | |||
EP1738798, | |||
EP1826778, | |||
EP1949404, | |||
EP2227295, | |||
EP2232961, | |||
EP2232962, | |||
EP2363170, | |||
EP2363171, | |||
FR2560421, | |||
FR2911843, | |||
GB957342, | |||
GB2015821, | |||
GB2361523, | |||
JP10071213, | |||
JP11047287, | |||
JP11102800, | |||
JP11243295, | |||
JP1276797, | |||
JP2000294399, | |||
JP2001129103, | |||
JP20016900, | |||
JP2002164686, | |||
JP2006233831, | |||
JP2007260939, | |||
JP2009515671, | |||
JP2011505191, | |||
JP2011505670, | |||
JP2011507151, | |||
JP4128717, | |||
JP4129768, | |||
JP4273409, | |||
JP4323267, | |||
JP4337300, | |||
JP494198, | |||
JP5046928, | |||
JP5341352, | |||
JP6036893, | |||
JP6180800, | |||
JP62150804, | |||
JP62186500, | |||
JP63149344, | |||
JP63218200, | |||
JP63226899, | |||
JP8173890, | |||
JP8264298, | |||
JP9162585, | |||
SU300137, | |||
SU569635, | |||
TW200930160, | |||
TW200934682, | |||
TW200939908, | |||
TW200940120, | |||
WO40064, | |||
WO49624, | |||
WO2007817, | |||
WO3039212, | |||
WO2001126569, | |||
WO2003092812, | |||
WO2004026401, | |||
WO2004101070, | |||
WO2006012467, | |||
WO2007061937, | |||
WO2007084701, | |||
WO2007130164, | |||
WO2007145906, | |||
WO2008030911, | |||
WO2009048745, | |||
WO2009070173, | |||
WO2009070588, | |||
WO2009073480, | |||
WO8607229, | |||
WO90012413, | |||
WO9203028, | |||
WO9302536, | |||
WO9817342, | |||
WO9939385, |
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