US20100230617A1 - Charged particle radiation therapy - Google Patents

Charged particle radiation therapy Download PDF

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US20100230617A1
US20100230617A1 US12/618,297 US61829709A US2010230617A1 US 20100230617 A1 US20100230617 A1 US 20100230617A1 US 61829709 A US61829709 A US 61829709A US 2010230617 A1 US2010230617 A1 US 2010230617A1
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accelerator
patient
gantry
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patient support
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Kenneth Gall
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Mevion Medical Systems Inc
Still River Systems Inc
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/10X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1077Beam delivery systems
    • A61N5/1081Rotating beam systems with a specific mechanical construction, e.g. gantries
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/10X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • HELECTRICITY
    • H05ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05HPLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H13/00Magnetic resonance accelerators; Cyclotrons
    • H05H13/02Synchrocyclotrons, i.e. frequency modulated cyclotrons
    • HELECTRICITY
    • H05ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05HPLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H13/00Magnetic resonance accelerators; Cyclotrons
    • H05H13/04Synchrotrons
    • HELECTRICITY
    • H05ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05HPLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H7/00Details of devices of the types covered by groups H05H9/00, H05H11/00, H05H13/00
    • H05H7/04Magnet systems, e.g. undulators, wigglers; Energisation thereof
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/10X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1085X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
    • A61N2005/1087Ions; Protons
    • HELECTRICITY
    • H05ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05HPLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
    • H05H7/00Details of devices of the types covered by groups H05H9/00, H05H11/00, H05H13/00
    • H05H7/04Magnet systems, e.g. undulators, wigglers; Energisation thereof
    • H05H2007/043Magnet systems, e.g. undulators, wigglers; Energisation thereof for beam focusing

Definitions

  • This description relates to charged particle (e.g., proton or ion) radiation therapy.
  • charged particle e.g., proton or ion
  • the energy of a proton or ion beam for therapy needs to be high compared to the energy of an electron beam used in conventional radiotherapy.
  • a proton beam, for example, that has a residual range of about 32 cm in water is considered adequate to treat any tumor target in the human population.
  • an initial proton beam energy of 250 MeV is needed to achieve the residual range of 32 cm.
  • particle accelerators can be used to produce a 250 MeV proton beam at a sufficient beam current (e.g., about 10 nA) for radiotherapy, including linear accelerators, synchrotrons, and cyclotrons.
  • the design of a proton or ion radiation therapy system for a clinical environment should take account of overall size, cost, and complexity. Available space is usually limited in crowded clinical environments. Lower cost allows more systems to be deployed to reach a broader patient population. Less complexity reduces operating costs and makes the system more reliable for routine clinical use.
  • the physician can more precisely relocate the intended target, relative to the patient's anatomy, at each treatment. Reliable reproduction of the patient's position for each treatment also can be aided using custom molds and braces fitted to the patient.
  • the radiotherapy beam can be directed into the patient from a succession of angles, so that, over the course of the treatment, the radiation dose at the target is enhanced while the extraneous radiation dose is spread over non-target tissues.
  • an isocentric gantry is rotated around the supine patient to direct the radiation beam along successive paths that lie at a range of angles in a common vertical plane toward a single point (called an isocenter) within the patient.
  • an isocenter By rotating the table on which the patient lies around a vertical axis, the beam can be directed into the patient along different paths.
  • Other techniques have been used to vary the position of the radiation source around the patient, including robotic manipulation. And other ways to move or reposition the patient have been used.
  • the x-ray beam may be directed toward the isocenter from an electron linear accelerator mounted on the gantry or robotic arm.
  • the circular particle accelerator that produces the beam is too large to mount on the gantry. Instead, the accelerator is mounted in a fixed position and the particle beam is redirected through a rotating gantry using magnetic beam steering elements. Blosser has proposed to mount an accelerator on the side of the gantry near the horizontal axis of rotation.
  • an accelerator is mounted on a gantry to enable the accelerator to move through a range of positions around a patient on a patient support.
  • the accelerator is configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range.
  • the proton or ion beam passes essentially directly from the accelerator housing to the patient.
  • Implementations may include one or more of the following features.
  • the gantry is supported for rotation on bearings on two sides of the patient support.
  • the gantry has two legs extending from an axis of rotation and a truss between the two legs on which the accelerator is mounted.
  • the gantry is constrained to rotate within a range of positions that is smaller than 360 degrees, at least as large as 180 degrees and in some implementations in the range from about 180 degrees to about 330 degrees. (A rotation range of 180 degrees is sufficient to provide for all angles of approach into a supine patient.)
  • Radio-protective walls include at least one wall that is not in line with the proton or ion beam from the accelerator in any of the positions within the range; that wall is constructed to provide the same radio-protection with less mass.
  • the patient support is mounted in an area that is accessible through a space defined by a range of positions at which the gantry is constrained not to rotate.
  • the patient support is movable relative to the gantry including rotation about a patient axis of rotation that is vertical.
  • the patient axis of rotation contains an isocenter in the vicinity of a patient on the patient support.
  • the gantry axis of rotation is horizontal and contains the isocenter.
  • the accelerator weighs less than 40 Tons and in typical implementations within a range from 5 to 30 tons, occupies a volume of less than 4.5 cubic meters and typically in a range from 0.7 to 4.5 cubic meters, and produces a proton or ion beam having an energy level of at least 150 MeV and in a range from 150 to 300 MeV, for example 250 MeV.
  • the accelerator can be a synchrocyclotron with a magnet structure that has a field strength of at least 6 Tesla and can be from 6 to 20 Tesla.
  • the magnet structure includes superconducting windings that are cooled by cryo-coolers.
  • the proton or ion beam passes directly from the accelerator to the general area of the patient stand.
  • a shielding chamber containing the patient support, the gantry, and the accelerator includes at least one wall of the chamber being thinner than other walls of the chamber. A portion of the chamber can be embedded within the earth.
  • an accelerator is configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in a patient.
  • the accelerator is small enough and lightweight enough to be mounted on a rotatable gantry in an orientation to permit the proton or ion beam to pass essentially directly from the accelerator housing to the patient.
  • a medical synchrocyclotron has a superconducting electromagnetic structure that generates a field strength of at least 6 Tesla, produces a beam of particles, such as protons, having an energy level of at least 150 MeV, has a volume no larger than 4.5 cubic meters, and has a weight less than 30 Tons.
  • a patient is supported within a treatment space, a beam of proton or ions pass in a straight line direction from an output of an accelerator to any arbitrary target within the patient, and the straight line direction is caused to be varied through a range of directions around the patient.
  • a structure in general, in an aspect, includes a patient support and a gantry on which an accelerator is mounted to enable the accelerator to move through a range of positions around a patient on the patient support.
  • the accelerator is configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range.
  • a walled enclosure contains the patient support, the gantry, and the accelerator. In some examples, more than half of the surface of the walled enclosure is embedded within the earth.
  • the size of the accelerator approaches 1.5 meter and the mass is reduced to about 15 to 20 tons.
  • the weight will depend on the stray magnetic field that is to be allowed near the accelerator. Even smaller weights and sizes may be possible.
  • This enables the cyclotron to be placed on a gantry, with the output beam aimed directly at the isocenter, and rotated around the patient, thus simplifying the delivery of proton or ion beam radiation therapy. All extracted beam focusing and steering elements are incorporated into the accelerator or immediately adjacent to it.
  • the direct mounting of the accelerator on the gantry eliminates beam transport elements that would otherwise be required to transport the beam from the accelerator to the target volume within the patient.
  • the size, complexity and cost of a proton or ion beam therapy system are reduced and its performance is improved. Reducing the range of rotation of the gantry to be less than 360 degrees in the vertical plane reduces the thickness of the shielding barrier that must be provided at locations to which the beam is never directed. It also allows for ease of access to the patient treatment space.
  • the synchrocyclotron can be scaled to arbitrarily high fields without compromising beam focusing during acceleration.
  • the elimination of cryogenic liquid cooled coils reduces the risk to the operator and the patient if vaporized liquid cryogen were to be released during a fault condition such as a magnet quench.
  • FIG. 1 is a perspective view of a therapy system.
  • FIG. 2 is an exploded perspective view of components of a synchrocyclotron.
  • FIGS. 3 , 4 , and 5 are cross-sectional views of a synchrocyclotron.
  • FIG. 6 is a perspective view of a synchrocyclotron.
  • FIG. 7 is a cross-sectional view of a portion of a reverse bobbin and windings.
  • FIG. 8 is a cross sectional view of a cable-in-channel composite conductor.
  • FIG. 9 is a cross-sectional view of an ion source.
  • FIG. 10 is a perspective view of a dee plate and a dummy dee.
  • FIG. 11 is a perspective view of a vault.
  • FIG. 12 is a perspective view of a treatment room with a vault.
  • FIG. 13 shows a profile of one-half of a symmetrical profile of a pole face and a pole piece.
  • a charged particle radiation therapy system 500 includes a beam-producing particle accelerator 502 having a weight and size small enough to permit it to be mounted on a rotating gantry 504 with its output directed straight (that is, essentially directly) from the accelerator housing toward a patient 506 .
  • the size and cost of the therapy system are significantly reduced and the reliability and precision of the system may be increased.
  • the steel gantry has two legs 508 , 510 mounted for rotation on two respective bearings 512 , 514 that lie on opposite sides of the patient.
  • the accelerator is supported by a steel truss 516 that is long enough to span a treatment area 518 in which the patient lies (e.g., twice as long as a tall person, to permit the person to be rotated fully within the space with any desired target area of the patient remaining in the line of the beam) and is attached stably at both ends to the rotating legs of the gantry.
  • the rotation of the gantry is limited to a range 520 of less than 360 degrees, e.g., about 180 degrees, to permit a floor 522 to extend from a wall of the vault 524 that houses the therapy system into the patient treatment area.
  • the limited rotation range of the gantry also reduces the required thickness of some of the walls (which never directly receive the beam, e.g., wall 530 ) which provide radiation shielding of people outside the treatment area.
  • a range of 180 degrees of gantry rotation is enough to cover all treatment approach angles, but providing a larger range of travel can be useful.
  • the range of rotation may usefully be between 180 and 330 degrees and still provide clearance for the therapy floor space.
  • the gantry may swing to positions that are hazardous to people or equipment positioned in a portion of the therapy space.
  • the horizontal rotational axis 532 of the gantry is located nominally one meter above the floor where the patient and therapist interact with the therapy system. This floor is positioned about 3 meters above the bottom floor of the therapy system shielded vault.
  • the accelerator can swing under the raised floor for delivery of treatment beams from below the rotational axis.
  • the patient couch moves and rotates in a substantially horizontal plane parallel to the rotational axis of the gantry.
  • the couch can rotate through a range 534 of about 270 degrees in the horizontal plane with this configuration. This combination of gantry and patient rotational ranges and degrees of freedom allow the therapist to select virtually any approach angle for the beam. If needed, the patient can be placed on the couch in the opposite orientation and then all possible angles can be used.
  • the accelerator uses a synchrocyclotron configuration having a very high magnetic field superconducting electromagnetic structure. Because the bend radius of a charged particle of a given kinetic energy is reduced in direct proportion to an increase in the magnetic field applied to it, the very high magnetic field superconducting magnetic structure permits the accelerator to be made smaller and lighter.
  • an isochronous cyclotron (in which the magnet is constructed to make the magnetic field stronger near the circumference than at the center to compensate for the mass increase and maintain a constant frequency of revolution) is impractical to use to achieve 250 MeV protons. This is because the angular variation in magnetic field used to maintain the beam focus in the isochronous cyclotron cannot be made large enough using iron pole face shaping.
  • the accelerator described here is a synchrocyclotron.
  • the synchrocyclotron uses a magnetic field that is uniform in rotation angle and falls off in strength with increasing radius. Such a field shape can be achieved regardless of the magnitude of the magnetic field, so in theory there is no upper limit to the magnetic field strength (and therefore the resulting particle energy at a fixed radius) that can be used in a synchrocyclotron.
  • Certain superconducting materials begin to lose their superconducting properties in the presence of very high magnetic fields.
  • High performance superconducting wire windings are used to allow very high magnetic fields to be achieved.
  • cryo-coolers are used to bring the superconducting coil windings to temperatures near absolute zero. Using cryo-coolers, rather than bath cooling the windings in liquid Helium, reduces complexity and cost.
  • the synchrocyclotron is supported on the gantry so that the beam is generated directly in line with the patient.
  • the gantry permits rotation of the cyclotron about a horizontal rotational axis that contains a point (isocenter 540 ) within or near the patient.
  • the split truss that is parallel to the rotational axis, supports the cyclotron on both sides.
  • a patient support area can be accommodated in a wide area around the isocenter.
  • a patient support table can be positioned to move relative to and to rotate about a vertical axis 542 through the isocenter so that, by a combination of gantry rotation and table motion and rotation, any angle of beam direction into any part of the patient can be achieved.
  • the two gantry arms are separated by more than twice the height of a tall patient, allowing the couch with patient to rotate and translate in a horizontal plane above the raised floor.
  • Limiting the gantry rotation angle allows for a reduction in the thickness of at least one of the walls surrounding the treatment room. Thick walls, typically constructed of concrete, provide radiation protection to individuals outside the treatment room. A wall downstream of a stopping proton beam needs to be about twice as thick as a wall at the opposite end of the room to provide an equivalent level of protection. Limiting the range of gantry rotation enables the treatment room to be sited below earth grade on three sides while allowing an occupied area adjacent to the thinnest wall reducing the cost of constructing the treatment room.
  • the superconducting synchrocyclotron 502 operates with a peak magnetic field in a pole gap of the synchrocyclotron of 8.8 Tesla.
  • the synchrocyclotron produces a beam of protons having an energy of 250 MeV.
  • the field strength could be in the range of 6 to 20 Tesla and the proton energy could be in the range of 150 to 300 MeV
  • the radiation therapy system described in this example is used for proton radiation therapy, but the same principles and details can be applied in analogous systems for use in heavy ion (ion) treatment systems.
  • an example synchrocyclotron 10 ( 502 in FIG. 1 ) includes a magnet system 12 that contains an ion source 90 , a radiofrequency drive system 91 , and a beam extraction system 38 .
  • the magnetic field established by the magnet system has a shape appropriate to maintain focus of a contained proton beam using a combination of a split pair of annular superconducting coils 40 , 42 and a pair of shaped ferromagnetic (e.g., low carbon steel) pole faces 44 , 46 .
  • the two superconducting magnet coils are centered on a common axis 47 and are spaced apart along the axis. As shown in FIGS. 7 and 8 , the coils are formed by of Nb3Sn-based superconducting 0.6 mm diameter strands 48 (that initially comprise a niobium-tin core surrounded by a copper sheath) deployed in a Rutherford cable-in-channel conductor geometry. After six individual strands are laid in a copper channel 50 , they are heated to cause a reaction that forms the final (brittle) material of the winding.
  • the wires are soldered into the copper channel (outer dimensions 3.02 ⁇ 1.96 mm and inner dimensions 2.05 ⁇ 1.27 mm) and covered with insulation 52 (in this example, a woven fiberglass material).
  • insulation 52 in this example, a woven fiberglass material.
  • the copper channel containing the wires 53 is then wound in a coil having a rectangular cross-section of 6.0 cm ⁇ 15.25 cm, having 30 layers and 47 turns per layer.
  • the wound coil is then vacuum impregnated with an epoxy compound 54 .
  • the finished coils are mounted on an annular stainless steel reverse bobbin 56 .
  • a heater blanket 55 is held against the inner face of the bobbin and the windings to protect the assembly in the event of a magnet quench.
  • the superconducting coil may be formed of 0.8 mm diameter Nb3Sn based strands. These strands can be deployed in a 4 strand cable, heat treated to form the superconducting matrix and soldered into a copper channel of outer dimension 3.19 by 2.57 mm.
  • the integrated cable in channel conductor can be insulated with overlapped woven fiberglass tape and then wound into coils of 49 turns and 26 layers deep with a rectangular cross section of 79.79 mm by 180.5 mm and inner radius of 374.65 mm.
  • the wound coil is then vacuum impregnated with an epoxy compound.
  • the entire coil can then be covered with copper sheets to provide thermal conductivity and mechanical stability and then contained in an additional layer of epoxy.
  • the precompression of the coil can be provided by heating the stainless steel reverse bobbin and fitting the coils within the reverse bobbin.
  • the reverse bobbin inner diameter is chosen so that when the entire mass is cooled to 4 K, the reverse bobbin stays in contact with the coil and provides some compression. Heating the stainless steel reverse bobbin to approximately 50 degrees C. and fitting coils at room temperature (20 degrees C.) can achieve this.
  • the geometry of the coil is maintained by mounting the coils in a “reverse” rectangular bobbin 56 and incorporating a pre-compression stainless steel bladder 58 between each coil and an inner face 57 of the bobbin to exert a restorative force 60 that works against the distorting force produced when the coils are energized.
  • the bladder is pre-compressed after the coils and the heater blanket are assembled on the bobbin, by injecting epoxy into the bladder and allowing it to harden.
  • the precompression force of the bladder is set to minimize the strain in the brittle Nb3Sn superconducting matrix through all phases of cool-down and magnet energizing.
  • the coil position is maintained relative to the magnet yoke and cryostat using a set of warm-to-cold support straps 402 , 404 , 406 .
  • Supporting the cold mass with thin straps minimizes the heat leakage imparted to the cold mass by the rigid support system.
  • the straps are arranged to withstand the varying gravitational force on the coil as the magnet rotates on board the gantry. They withstand the combined effects of gravity and the large de-centering force realized by the coil when it is perturbed from a perfectly symmetric position relative to the magnet yoke. Additionally the links act to minimize the dynamic forces imparted on the coil as the gantry accelerates and decelerates when the position is changed.
  • Each warm-to-cold support includes 3 S 2 fiberglass links. Two links 410 , 412 are supported across pins between the warm yoke and an intermediate temperature (50-70 K), and one link 408 is supported across the intermediate temperature pin and a pin attached to the cold mass. Each link is 10.2 cm long (pin center to pin center) and is 20 mm wide. The link thickness is 1.59 mm. Each pin is made of stainless steel and is 47.7 mm in diameter.
  • the field strength profile as a function of radius is determined largely by choice of coil geometry; the pole faces 44 , 46 of the permeable yoke material can be contoured to fine tune the shape of the magnetic field to insure that the particle beam remains focused during acceleration.
  • the superconducting coils are maintained at temperatures near absolute zero (e.g., about 4 degrees Kelvin) by enclosing the coil assembly (the coils and the bobbin) inside an evacuated annular aluminum or stainless steel cryostatic chamber 70 that provides a free space around the coil structure, except at a limited set of support points 71 , 73 .
  • the outer wall of the cryostat may be made of low carbon steel to provide an additional return flux path for the magnetic field.
  • the temperature near absolute zero is achieved and maintained using two Gifford-McMahon cryo-coolers 72 , 74 that are arranged at different positions on the coil assembly. Each cryo-cooler has a cold end 76 in contact with the coil assembly.
  • cryo-cooler heads 78 are supplied with compressed Helium from a compressor 80 .
  • Two other Gifford-McMahon cryo-coolers 77 , 79 are arranged to cool high temperature (e.g., 60-80 degrees Kelvin) leads 81 that supply current to the superconducting windings.
  • the coil assembly and cryostatic chambers are mounted within and fully enclosed by two halves 81 , 83 of a pillbox-shaped magnet yoke 82 .
  • the inner diameter of the coil assembly is about 140 cm.
  • the iron yoke 82 provides a path for the return magnetic field flux 84 and magnetically shields the volume 86 between the pole faces 44 , 46 to prevent external magnetic influences from perturbing the shape of the magnetic field within that volume.
  • the yoke also serves to decrease the stray magnetic field in the vicinity of the accelerator.
  • the synchrocyclotron includes an ion source 90 of a Penning ion gauge geometry located near the geometric center 92 of the magnet structure 82 .
  • the ion source is fed from a supply 99 of hydrogen through a gas line 101 and tube 194 that delivers gaseous hydrogen.
  • Electric cables 94 carry an electric current from a current source 95 to stimulate electron discharge from cathodes 192 , 194 that are aligned with the magnetic field, 200 .
  • the discharged electrons ionize the gas exiting through a small hole from tube 194 to create a supply of positive ions (protons) for acceleration by one semicircular (dee-shaped) radio-frequency plate 100 that spans half of the space enclosed by the magnet structure and one dummy dee plate 102 .
  • the dee plate 100 is a hollow metal structure that has two semicircular surfaces 103 , 105 that enclose a space 107 in which the protons are accelerated during half of their rotation around the space enclosed by the magnet structure.
  • a duct 109 opening into the space 107 extends through the yoke to an external location from which a vacuum pump 111 can be attached to evacuate the space 107 and the rest of the space within a vacuum chamber 119 in which the acceleration takes place.
  • the dummy dee 102 comprises a rectangular metal ring that is spaced near to the exposed rim of the dee plate. The dummy dee is grounded to the vacuum chamber and magnet yoke.
  • the dee plate 100 is driven by a radio-frequency signal that is applied at the end of a radio-frequency transmission line to impart an electric field in the space 107 .
  • the radiofrequency electric field is made to vary in time as the accelerated particle beam increases in distance from the geometric center.
  • radio frequency waveform generators Examples of radio frequency waveform generators that are useful for this purpose are described in U.S. patent application Ser. No. 11/187,633, titled “A Programmable Radio Frequency Waveform Generator for a Synchrocyclotron,” filed Jul. 21, 2005, and in U.S. provisional patent application Ser. 60/590,089, same title, filed on Jul. 21, 2004, both of which are incorporated in their entirety by this reference.
  • the magnet structure is arranged to reduce the capacitance between the radio frequency plates and ground. This is done by forming holes with sufficient clearance from the radiofrequency structures through the outer yoke and the cryostat housing and making sufficient space between the magnet pole faces.
  • the high voltage alternating potential that drives the dee plate has a frequency that is swept downward during the accelerating cycle to account for the increasing relativistic mass of the protons and the decreasing magnetic field.
  • the dummy dee does not require a hollow semi-cylindrical structure as it is at ground potential along with the vacuum chamber walls.
  • Other plate arrangements could be used such as more than one pair of accelerating electrodes driven with different electrical phases or multiples of the fundamental frequency.
  • the RF structure can be tuned to keep the Q high during the required frequency sweep by using, for example, a rotating capacitor having intermeshing rotating and stationary blades. During each meshing of the blades, the capacitance increases, thus lowering the resonant frequency of the RF structure.
  • the blades can be shaped to create a precise frequency sweep required.
  • a drive motor for the rotating condenser can be phase locked to the RF generator for precise control. One bunch of particles is accelerated during each meshing of the blades of the rotating condenser.
  • the vacuum chamber 119 in which the acceleration occurs is a generally cylindrical container that is thinner in the center and thicker at the rim.
  • the vacuum chamber encloses the RF plates and the ion source and is evacuated by the vacuum pump 111 . Maintaining a high vacuum insures that accelerating ions are not lost to collisions with gas molecules and enables the RF voltage to be kept at a higher level without arcing to ground.
  • Protons traverse a generally spiral path beginning at the ion source. In half of each loop of the spiral path, the protons gain energy as they pass through the RF electric field in space 107 . As the ions gain energy, the radius of the central orbit of each successive loop of their spiral path is larger than the prior loop until the loop radius reaches the maximum radius of the pole face. At that location a magnetic and electric field perturbation directs ions into an area where the magnetic field rapidly decreases, and the ions depart the area of the high magnetic field and are directed through an evacuated tube 38 to exit the yoke of the cyclotron. The ions exiting the cyclotron will tend to disperse as they enter the area of markedly decreased magnetic field that exists in the room around the cyclotron. Beam shaping elements 107 , 109 in the extraction channel 38 redirect the ions so that they stay in a straight beam of limited spatial extent.
  • the magnetic field within the pole gap needs to have certain properties to maintain the beam within the evacuated chamber as it accelerates.
  • n ⁇ ( r/B ) dB/dr
  • the ferromagnetic pole face is designed to shape the magnetic field generated by the coils so that the field index n is maintained positive and less than 0.2 in the smallest diameter consistent with a 250 MeV beam in the given magnetic field.
  • a beam formation system 125 that can be programmably controlled to create a desired combination of scattering angle and range modulation for the beam.
  • Examples of beam forming systems useful for that purpose are described in U.S. patent application Ser. No. 10/949,734, titled “A Programmable Particle Scatterer for Radiation Therapy Beam Formation”, filed Sep. 24, 2004, and U.S. provisional patent application Ser. 60/590,088, filed Jul. 21, 2005, both of which are incorporated in their entirety by this reference.
  • the plates absorb energy from the applied radio frequency field as a result of conductive resistance along the surfaces of the plates. This energy appears as heat and is removed from the plates using water cooling lines 108 that release the heat in a heat exchanger 113 .
  • the separate magnetic shield includes of a layer 117 of ferromagnetic material (e.g., steel or iron) that encloses the pillbox yoke, separated by a space 116 .
  • This configuration that includes a sandwich of a yoke, a space, and a shield achieves adequate shielding for a given leakage magnetic field at lower weight.
  • the gantry allows the synchrocyclotron to be rotated about the horizontal rotational axis 532 .
  • the truss structure 516 has two generally parallel spans 580 , 582 .
  • the synchrocyclotron is cradled between the spans about midway between the legs.
  • the gantry is balanced for rotation about the bearings using counterweights 122 , 124 mounted on ends of the legs opposite the truss.
  • the gantry is driven to rotate by an electric motor mounted to one of the gantry legs and connected to the bearing housings by drive gears and belts or chains.
  • the rotational position of the gantry is derived from signals provided by shaft angle encoders incorporated into the gantry drive motors and the drive gears.
  • the beam formation system 125 acts on the ion beam to give it properties suitable for patient treatment.
  • the beam may be spread and its depth of penetration varied to provide uniform radiation across a given target volume.
  • the beam formation system can include passive scattering elements as well as active scanning elements.
  • synchrocyclotron All of the active systems of the synchrocyclotron (the current driven superconducting coils, the RF-driven plates, the vacuum pumps for the vacuum acceleration chamber and for the superconducting coil cooling chamber, the current driven ion source, the hydrogen gas source, and the RF plate coolers, for example), are controlled by appropriate synchrocyclotron control electronics (not shown).
  • the control of the gantry, the patient support, the active beam shaping elements, and the synchrocyclotron to perform a therapy session is achieved by appropriate therapy control electronics (not shown).
  • the gantry bearings are supported by the walls of a cyclotron vault 524 .
  • the gantry enables the cyclotron to be swung through a range 520 of 180 degrees (or more) including positions above, to the side of, and below the patient.
  • the vault is tall enough to clear the gantry at the top and bottom extremes of its motion.
  • a maze 146 sided by walls 148 , 150 provides an entry and exit route for therapists and patients. Because at least one wall 152 is never in line with the proton beam directly from the cyclotron, it can be made relatively thin and still perform its shielding function.
  • the other three side walls 154 , 156 , 150 / 148 of the room which may need to be more heavily shielded, can be buried within an earthen hill (not shown).
  • the required thickness of walls 154 , 156 , and 158 can be reduced, because the earth can itself provide some of the needed shielding.
  • a therapy room 160 is constructed within the vault.
  • the therapy room is cantilevered from walls 154 , 156 , 150 and the base 162 of the containing room into the space between the gantry legs in a manner that clears the swinging gantry and also maximizes the extent of the floor space 164 of the therapy room.
  • Periodic servicing of the accelerator can be accomplished in the space below the raised floor.
  • Power supplies, cooling equipment, vacuum pumps and other support equipment can be located under the raised floor in this separate space.
  • the patient support 170 can be mounted in a variety of ways that permit the support to be raised and lowered and the patient to be rotated and moved to a variety of positions and orientations.

Abstract

Among other things, an accelerator is mounted on a gantry to enable the accelerator to move through a range of positions around a patient on a patient support. The accelerator is configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range. The proton or ion beam passes essentially directly from the accelerator to the patient. In some examples, the synchrocyclotron has a superconducting electromagnetic structure that generates a field strength of at least 6 Tesla, produces a beam of particles having an energy level of at least 150 MeV, has a volume no larger than 4.5 cubic meters, and has a weight less than 30 Tons.

Description

  • This application is entitled to the benefit of the filing date of U.S. provisional patent application Ser. No. 60/738,404, filed Nov. 18, 2005, the entire text of which is incorporated by reference here.
  • BACKGROUND
  • This description relates to charged particle (e.g., proton or ion) radiation therapy.
  • The energy of a proton or ion beam for therapy needs to be high compared to the energy of an electron beam used in conventional radiotherapy. A proton beam, for example, that has a residual range of about 32 cm in water is considered adequate to treat any tumor target in the human population. When allowance is made for the reduction in residual range that results from scattering foils used to spread the beam, an initial proton beam energy of 250 MeV is needed to achieve the residual range of 32 cm.
  • Several kinds of particle accelerators can be used to produce a 250 MeV proton beam at a sufficient beam current (e.g., about 10 nA) for radiotherapy, including linear accelerators, synchrotrons, and cyclotrons.
  • The design of a proton or ion radiation therapy system for a clinical environment should take account of overall size, cost, and complexity. Available space is usually limited in crowded clinical environments. Lower cost allows more systems to be deployed to reach a broader patient population. Less complexity reduces operating costs and makes the system more reliable for routine clinical use.
  • Other considerations also bear on the design of such a therapy system. By configuring the system to apply the treatment to patients who are held in a stable, reproducible position (for example, lying supine on a flat table), the physician can more precisely relocate the intended target, relative to the patient's anatomy, at each treatment. Reliable reproduction of the patient's position for each treatment also can be aided using custom molds and braces fitted to the patient. With a patient in a stable, fixed position, the radiotherapy beam can be directed into the patient from a succession of angles, so that, over the course of the treatment, the radiation dose at the target is enhanced while the extraneous radiation dose is spread over non-target tissues.
  • Traditionally, an isocentric gantry is rotated around the supine patient to direct the radiation beam along successive paths that lie at a range of angles in a common vertical plane toward a single point (called an isocenter) within the patient. By rotating the table on which the patient lies around a vertical axis, the beam can be directed into the patient along different paths. Other techniques have been used to vary the position of the radiation source around the patient, including robotic manipulation. And other ways to move or reposition the patient have been used.
  • In high energy x-ray beam therapy, the x-ray beam may be directed toward the isocenter from an electron linear accelerator mounted on the gantry or robotic arm.
  • In typical proton beam therapy, the circular particle accelerator that produces the beam is too large to mount on the gantry. Instead, the accelerator is mounted in a fixed position and the particle beam is redirected through a rotating gantry using magnetic beam steering elements. Blosser has proposed to mount an accelerator on the side of the gantry near the horizontal axis of rotation.
  • SUMMARY
  • In general, in one aspect, an accelerator is mounted on a gantry to enable the accelerator to move through a range of positions around a patient on a patient support. The accelerator is configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range. The proton or ion beam passes essentially directly from the accelerator housing to the patient.
  • Implementations may include one or more of the following features. The gantry is supported for rotation on bearings on two sides of the patient support. The gantry has two legs extending from an axis of rotation and a truss between the two legs on which the accelerator is mounted. The gantry is constrained to rotate within a range of positions that is smaller than 360 degrees, at least as large as 180 degrees and in some implementations in the range from about 180 degrees to about 330 degrees. (A rotation range of 180 degrees is sufficient to provide for all angles of approach into a supine patient.) Radio-protective walls include at least one wall that is not in line with the proton or ion beam from the accelerator in any of the positions within the range; that wall is constructed to provide the same radio-protection with less mass. The patient support is mounted in an area that is accessible through a space defined by a range of positions at which the gantry is constrained not to rotate. The patient support is movable relative to the gantry including rotation about a patient axis of rotation that is vertical. The patient axis of rotation contains an isocenter in the vicinity of a patient on the patient support. The gantry axis of rotation is horizontal and contains the isocenter. The accelerator weighs less than 40 Tons and in typical implementations within a range from 5 to 30 tons, occupies a volume of less than 4.5 cubic meters and typically in a range from 0.7 to 4.5 cubic meters, and produces a proton or ion beam having an energy level of at least 150 MeV and in a range from 150 to 300 MeV, for example 250 MeV.
  • The accelerator can be a synchrocyclotron with a magnet structure that has a field strength of at least 6 Tesla and can be from 6 to 20 Tesla. The magnet structure includes superconducting windings that are cooled by cryo-coolers. The proton or ion beam passes directly from the accelerator to the general area of the patient stand. A shielding chamber containing the patient support, the gantry, and the accelerator includes at least one wall of the chamber being thinner than other walls of the chamber. A portion of the chamber can be embedded within the earth.
  • In general, in one aspect, an accelerator is configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in a patient. The accelerator is small enough and lightweight enough to be mounted on a rotatable gantry in an orientation to permit the proton or ion beam to pass essentially directly from the accelerator housing to the patient.
  • In general, in one aspect, a medical synchrocyclotron has a superconducting electromagnetic structure that generates a field strength of at least 6 Tesla, produces a beam of particles, such as protons, having an energy level of at least 150 MeV, has a volume no larger than 4.5 cubic meters, and has a weight less than 30 Tons.
  • In general, in one aspect, a patient is supported within a treatment space, a beam of proton or ions pass in a straight line direction from an output of an accelerator to any arbitrary target within the patient, and the straight line direction is caused to be varied through a range of directions around the patient.
  • In general, in an aspect, a structure includes a patient support and a gantry on which an accelerator is mounted to enable the accelerator to move through a range of positions around a patient on the patient support. The accelerator is configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range. A walled enclosure contains the patient support, the gantry, and the accelerator. In some examples, more than half of the surface of the walled enclosure is embedded within the earth.
  • Other aspects include other combinations of the aspects and features discussed above and other features expressed as apparatus, systems, methods, software products, business methods, and in other ways.
  • By generating a magnetic field of about 10 Tesla, the size of the accelerator approaches 1.5 meter and the mass is reduced to about 15 to 20 tons. The weight will depend on the stray magnetic field that is to be allowed near the accelerator. Even smaller weights and sizes may be possible. This enables the cyclotron to be placed on a gantry, with the output beam aimed directly at the isocenter, and rotated around the patient, thus simplifying the delivery of proton or ion beam radiation therapy. All extracted beam focusing and steering elements are incorporated into the accelerator or immediately adjacent to it. The direct mounting of the accelerator on the gantry eliminates beam transport elements that would otherwise be required to transport the beam from the accelerator to the target volume within the patient. The size, complexity and cost of a proton or ion beam therapy system are reduced and its performance is improved. Reducing the range of rotation of the gantry to be less than 360 degrees in the vertical plane reduces the thickness of the shielding barrier that must be provided at locations to which the beam is never directed. It also allows for ease of access to the patient treatment space. The synchrocyclotron can be scaled to arbitrarily high fields without compromising beam focusing during acceleration. The elimination of cryogenic liquid cooled coils reduces the risk to the operator and the patient if vaporized liquid cryogen were to be released during a fault condition such as a magnet quench.
  • Other advantages and features will become apparent from the following description and from the claims.
  • DESCRIPTION OF DRAWINGS
  • FIG. 1 is a perspective view of a therapy system.
  • FIG. 2 is an exploded perspective view of components of a synchrocyclotron.
  • FIGS. 3, 4, and 5 are cross-sectional views of a synchrocyclotron.
  • FIG. 6 is a perspective view of a synchrocyclotron.
  • FIG. 7 is a cross-sectional view of a portion of a reverse bobbin and windings.
  • FIG. 8 is a cross sectional view of a cable-in-channel composite conductor.
  • FIG. 9 is a cross-sectional view of an ion source.
  • FIG. 10 is a perspective view of a dee plate and a dummy dee.
  • FIG. 11 is a perspective view of a vault.
  • FIG. 12 is a perspective view of a treatment room with a vault.
  • FIG. 13 shows a profile of one-half of a symmetrical profile of a pole face and a pole piece.
  • DETAILED DESCRIPTION
  • As shown in FIG. 1, a charged particle radiation therapy system 500 includes a beam-producing particle accelerator 502 having a weight and size small enough to permit it to be mounted on a rotating gantry 504 with its output directed straight (that is, essentially directly) from the accelerator housing toward a patient 506. The size and cost of the therapy system are significantly reduced and the reliability and precision of the system may be increased.
  • In some implementations, the steel gantry has two legs 508, 510 mounted for rotation on two respective bearings 512, 514 that lie on opposite sides of the patient. The accelerator is supported by a steel truss 516 that is long enough to span a treatment area 518 in which the patient lies (e.g., twice as long as a tall person, to permit the person to be rotated fully within the space with any desired target area of the patient remaining in the line of the beam) and is attached stably at both ends to the rotating legs of the gantry.
  • In some examples, the rotation of the gantry is limited to a range 520 of less than 360 degrees, e.g., about 180 degrees, to permit a floor 522 to extend from a wall of the vault 524 that houses the therapy system into the patient treatment area. The limited rotation range of the gantry also reduces the required thickness of some of the walls (which never directly receive the beam, e.g., wall 530) which provide radiation shielding of people outside the treatment area. A range of 180 degrees of gantry rotation is enough to cover all treatment approach angles, but providing a larger range of travel can be useful. For example the range of rotation may usefully be between 180 and 330 degrees and still provide clearance for the therapy floor space. When the range of travel is large, the gantry may swing to positions that are hazardous to people or equipment positioned in a portion of the therapy space.
  • The horizontal rotational axis 532 of the gantry is located nominally one meter above the floor where the patient and therapist interact with the therapy system. This floor is positioned about 3 meters above the bottom floor of the therapy system shielded vault. The accelerator can swing under the raised floor for delivery of treatment beams from below the rotational axis. The patient couch moves and rotates in a substantially horizontal plane parallel to the rotational axis of the gantry. The couch can rotate through a range 534 of about 270 degrees in the horizontal plane with this configuration. This combination of gantry and patient rotational ranges and degrees of freedom allow the therapist to select virtually any approach angle for the beam. If needed, the patient can be placed on the couch in the opposite orientation and then all possible angles can be used.
  • In some implementations, the accelerator uses a synchrocyclotron configuration having a very high magnetic field superconducting electromagnetic structure. Because the bend radius of a charged particle of a given kinetic energy is reduced in direct proportion to an increase in the magnetic field applied to it, the very high magnetic field superconducting magnetic structure permits the accelerator to be made smaller and lighter.
  • For an average magnetic field strength larger than about 5 Tesla, an isochronous cyclotron (in which the magnet is constructed to make the magnetic field stronger near the circumference than at the center to compensate for the mass increase and maintain a constant frequency of revolution) is impractical to use to achieve 250 MeV protons. This is because the angular variation in magnetic field used to maintain the beam focus in the isochronous cyclotron cannot be made large enough using iron pole face shaping.
  • The accelerator described here is a synchrocyclotron. The synchrocyclotron uses a magnetic field that is uniform in rotation angle and falls off in strength with increasing radius. Such a field shape can be achieved regardless of the magnitude of the magnetic field, so in theory there is no upper limit to the magnetic field strength (and therefore the resulting particle energy at a fixed radius) that can be used in a synchrocyclotron.
  • Certain superconducting materials begin to lose their superconducting properties in the presence of very high magnetic fields. High performance superconducting wire windings are used to allow very high magnetic fields to be achieved.
  • Superconducting materials typically need to be cooled to low temperatures for their superconducting properties to be realized. In some examples described here, cryo-coolers are used to bring the superconducting coil windings to temperatures near absolute zero. Using cryo-coolers, rather than bath cooling the windings in liquid Helium, reduces complexity and cost.
  • The synchrocyclotron is supported on the gantry so that the beam is generated directly in line with the patient. The gantry permits rotation of the cyclotron about a horizontal rotational axis that contains a point (isocenter 540) within or near the patient. The split truss that is parallel to the rotational axis, supports the cyclotron on both sides.
  • Because the rotational range of the gantry is limited, a patient support area can be accommodated in a wide area around the isocenter. Because the floor can be extended broadly around the isocenter, a patient support table can be positioned to move relative to and to rotate about a vertical axis 542 through the isocenter so that, by a combination of gantry rotation and table motion and rotation, any angle of beam direction into any part of the patient can be achieved. The two gantry arms are separated by more than twice the height of a tall patient, allowing the couch with patient to rotate and translate in a horizontal plane above the raised floor.
  • Limiting the gantry rotation angle allows for a reduction in the thickness of at least one of the walls surrounding the treatment room. Thick walls, typically constructed of concrete, provide radiation protection to individuals outside the treatment room. A wall downstream of a stopping proton beam needs to be about twice as thick as a wall at the opposite end of the room to provide an equivalent level of protection. Limiting the range of gantry rotation enables the treatment room to be sited below earth grade on three sides while allowing an occupied area adjacent to the thinnest wall reducing the cost of constructing the treatment room.
  • In the example implementation shown in FIG. 1, the superconducting synchrocyclotron 502 operates with a peak magnetic field in a pole gap of the synchrocyclotron of 8.8 Tesla. The synchrocyclotron produces a beam of protons having an energy of 250 MeV. In other implementations the field strength could be in the range of 6 to 20 Tesla and the proton energy could be in the range of 150 to 300 MeV
  • The radiation therapy system described in this example is used for proton radiation therapy, but the same principles and details can be applied in analogous systems for use in heavy ion (ion) treatment systems.
  • As shown in FIGS. 2, 3, 4, 5, and 6, an example synchrocyclotron 10 (502 in FIG. 1) includes a magnet system 12 that contains an ion source 90, a radiofrequency drive system 91, and a beam extraction system 38. The magnetic field established by the magnet system has a shape appropriate to maintain focus of a contained proton beam using a combination of a split pair of annular superconducting coils 40, 42 and a pair of shaped ferromagnetic (e.g., low carbon steel) pole faces 44, 46.
  • The two superconducting magnet coils are centered on a common axis 47 and are spaced apart along the axis. As shown in FIGS. 7 and 8, the coils are formed by of Nb3Sn-based superconducting 0.6 mm diameter strands 48 (that initially comprise a niobium-tin core surrounded by a copper sheath) deployed in a Rutherford cable-in-channel conductor geometry. After six individual strands are laid in a copper channel 50, they are heated to cause a reaction that forms the final (brittle) material of the winding. After the material has been reacted, the wires are soldered into the copper channel (outer dimensions 3.02×1.96 mm and inner dimensions 2.05×1.27 mm) and covered with insulation 52 (in this example, a woven fiberglass material). The copper channel containing the wires 53 is then wound in a coil having a rectangular cross-section of 6.0 cm×15.25 cm, having 30 layers and 47 turns per layer. The wound coil is then vacuum impregnated with an epoxy compound 54. The finished coils are mounted on an annular stainless steel reverse bobbin 56. A heater blanket 55 is held against the inner face of the bobbin and the windings to protect the assembly in the event of a magnet quench. In an alternate version the superconducting coil may be formed of 0.8 mm diameter Nb3Sn based strands. These strands can be deployed in a 4 strand cable, heat treated to form the superconducting matrix and soldered into a copper channel of outer dimension 3.19 by 2.57 mm. The integrated cable in channel conductor can be insulated with overlapped woven fiberglass tape and then wound into coils of 49 turns and 26 layers deep with a rectangular cross section of 79.79 mm by 180.5 mm and inner radius of 374.65 mm. The wound coil is then vacuum impregnated with an epoxy compound. The entire coil can then be covered with copper sheets to provide thermal conductivity and mechanical stability and then contained in an additional layer of epoxy. The precompression of the coil can be provided by heating the stainless steel reverse bobbin and fitting the coils within the reverse bobbin. The reverse bobbin inner diameter is chosen so that when the entire mass is cooled to 4 K, the reverse bobbin stays in contact with the coil and provides some compression. Heating the stainless steel reverse bobbin to approximately 50 degrees C. and fitting coils at room temperature (20 degrees C.) can achieve this.
  • The geometry of the coil is maintained by mounting the coils in a “reverse” rectangular bobbin 56 and incorporating a pre-compression stainless steel bladder 58 between each coil and an inner face 57 of the bobbin to exert a restorative force 60 that works against the distorting force produced when the coils are energized. The bladder is pre-compressed after the coils and the heater blanket are assembled on the bobbin, by injecting epoxy into the bladder and allowing it to harden. The precompression force of the bladder is set to minimize the strain in the brittle Nb3Sn superconducting matrix through all phases of cool-down and magnet energizing.
  • As shown in FIG. 5, the coil position is maintained relative to the magnet yoke and cryostat using a set of warm-to-cold support straps 402, 404, 406. Supporting the cold mass with thin straps minimizes the heat leakage imparted to the cold mass by the rigid support system. The straps are arranged to withstand the varying gravitational force on the coil as the magnet rotates on board the gantry. They withstand the combined effects of gravity and the large de-centering force realized by the coil when it is perturbed from a perfectly symmetric position relative to the magnet yoke. Additionally the links act to minimize the dynamic forces imparted on the coil as the gantry accelerates and decelerates when the position is changed. Each warm-to-cold support includes 3 S2 fiberglass links. Two links 410, 412 are supported across pins between the warm yoke and an intermediate temperature (50-70 K), and one link 408 is supported across the intermediate temperature pin and a pin attached to the cold mass. Each link is 10.2 cm long (pin center to pin center) and is 20 mm wide. The link thickness is 1.59 mm. Each pin is made of stainless steel and is 47.7 mm in diameter.
  • As shown in FIG. 13, the field strength profile as a function of radius is determined largely by choice of coil geometry; the pole faces 44, 46 of the permeable yoke material can be contoured to fine tune the shape of the magnetic field to insure that the particle beam remains focused during acceleration.
  • The superconducting coils are maintained at temperatures near absolute zero (e.g., about 4 degrees Kelvin) by enclosing the coil assembly (the coils and the bobbin) inside an evacuated annular aluminum or stainless steel cryostatic chamber 70 that provides a free space around the coil structure, except at a limited set of support points 71, 73. In an alternate version the outer wall of the cryostat may be made of low carbon steel to provide an additional return flux path for the magnetic field. The temperature near absolute zero is achieved and maintained using two Gifford-McMahon cryo- coolers 72, 74 that are arranged at different positions on the coil assembly. Each cryo-cooler has a cold end 76 in contact with the coil assembly. The cryo-cooler heads 78 are supplied with compressed Helium from a compressor 80. Two other Gifford-McMahon cryo- coolers 77, 79 are arranged to cool high temperature (e.g., 60-80 degrees Kelvin) leads 81 that supply current to the superconducting windings.
  • The coil assembly and cryostatic chambers are mounted within and fully enclosed by two halves 81, 83 of a pillbox-shaped magnet yoke 82. In this example, the inner diameter of the coil assembly is about 140 cm. The iron yoke 82 provides a path for the return magnetic field flux 84 and magnetically shields the volume 86 between the pole faces 44, 46 to prevent external magnetic influences from perturbing the shape of the magnetic field within that volume. The yoke also serves to decrease the stray magnetic field in the vicinity of the accelerator.
  • As shown in FIGS. 3 and 9, the synchrocyclotron includes an ion source 90 of a Penning ion gauge geometry located near the geometric center 92 of the magnet structure 82. The ion source is fed from a supply 99 of hydrogen through a gas line 101 and tube 194 that delivers gaseous hydrogen. Electric cables 94 carry an electric current from a current source 95 to stimulate electron discharge from cathodes 192, 194 that are aligned with the magnetic field, 200.
  • The discharged electrons ionize the gas exiting through a small hole from tube 194 to create a supply of positive ions (protons) for acceleration by one semicircular (dee-shaped) radio-frequency plate 100 that spans half of the space enclosed by the magnet structure and one dummy dee plate 102. As shown in FIG. 10, the dee plate 100 is a hollow metal structure that has two semicircular surfaces 103, 105 that enclose a space 107 in which the protons are accelerated during half of their rotation around the space enclosed by the magnet structure. A duct 109 opening into the space 107 extends through the yoke to an external location from which a vacuum pump 111 can be attached to evacuate the space 107 and the rest of the space within a vacuum chamber 119 in which the acceleration takes place. The dummy dee 102 comprises a rectangular metal ring that is spaced near to the exposed rim of the dee plate. The dummy dee is grounded to the vacuum chamber and magnet yoke. The dee plate 100 is driven by a radio-frequency signal that is applied at the end of a radio-frequency transmission line to impart an electric field in the space 107. The radiofrequency electric field is made to vary in time as the accelerated particle beam increases in distance from the geometric center. Examples of radio frequency waveform generators that are useful for this purpose are described in U.S. patent application Ser. No. 11/187,633, titled “A Programmable Radio Frequency Waveform Generator for a Synchrocyclotron,” filed Jul. 21, 2005, and in U.S. provisional patent application Ser. 60/590,089, same title, filed on Jul. 21, 2004, both of which are incorporated in their entirety by this reference.
  • For the beam emerging from the centrally located ion source to clear the ion source structure as it begins to spiral outward, a large voltage difference is required across the radiofrequency plates. 20,000 Volts is applied across the radiofrequency plates. In some versions from 8,000 to 20,000 Volts may be applied across the radiofrequency plates. To reduce the power required to drive this large voltage, the magnet structure is arranged to reduce the capacitance between the radio frequency plates and ground. This is done by forming holes with sufficient clearance from the radiofrequency structures through the outer yoke and the cryostat housing and making sufficient space between the magnet pole faces.
  • The high voltage alternating potential that drives the dee plate has a frequency that is swept downward during the accelerating cycle to account for the increasing relativistic mass of the protons and the decreasing magnetic field. The dummy dee does not require a hollow semi-cylindrical structure as it is at ground potential along with the vacuum chamber walls. Other plate arrangements could be used such as more than one pair of accelerating electrodes driven with different electrical phases or multiples of the fundamental frequency. The RF structure can be tuned to keep the Q high during the required frequency sweep by using, for example, a rotating capacitor having intermeshing rotating and stationary blades. During each meshing of the blades, the capacitance increases, thus lowering the resonant frequency of the RF structure. The blades can be shaped to create a precise frequency sweep required. A drive motor for the rotating condenser can be phase locked to the RF generator for precise control. One bunch of particles is accelerated during each meshing of the blades of the rotating condenser.
  • The vacuum chamber 119 in which the acceleration occurs is a generally cylindrical container that is thinner in the center and thicker at the rim. The vacuum chamber encloses the RF plates and the ion source and is evacuated by the vacuum pump 111. Maintaining a high vacuum insures that accelerating ions are not lost to collisions with gas molecules and enables the RF voltage to be kept at a higher level without arcing to ground.
  • Protons traverse a generally spiral path beginning at the ion source. In half of each loop of the spiral path, the protons gain energy as they pass through the RF electric field in space 107. As the ions gain energy, the radius of the central orbit of each successive loop of their spiral path is larger than the prior loop until the loop radius reaches the maximum radius of the pole face. At that location a magnetic and electric field perturbation directs ions into an area where the magnetic field rapidly decreases, and the ions depart the area of the high magnetic field and are directed through an evacuated tube 38 to exit the yoke of the cyclotron. The ions exiting the cyclotron will tend to disperse as they enter the area of markedly decreased magnetic field that exists in the room around the cyclotron. Beam shaping elements 107, 109 in the extraction channel 38 redirect the ions so that they stay in a straight beam of limited spatial extent.
  • The magnetic field within the pole gap needs to have certain properties to maintain the beam within the evacuated chamber as it accelerates. The magnetic field index

  • n=−(r/B)dB/dr
  • must be kept positive to maintain this “weak” focusing. Here r is the radius of the beam and B is the magnetic field. Additionally the field index needs to be maintained below 0.2, because at this value the periodicity of radial oscillations and vertical oscillations of the beam coincide in a νr=2 ν2 resonance. The betatron frequencies are defined by νr=(1−n)1/2 and νz=n1/2 The ferromagnetic pole face is designed to shape the magnetic field generated by the coils so that the field index n is maintained positive and less than 0.2 in the smallest diameter consistent with a 250 MeV beam in the given magnetic field.
  • As the beam exits the extraction channel it is passed through a beam formation system 125 that can be programmably controlled to create a desired combination of scattering angle and range modulation for the beam. Examples of beam forming systems useful for that purpose are described in U.S. patent application Ser. No. 10/949,734, titled “A Programmable Particle Scatterer for Radiation Therapy Beam Formation”, filed Sep. 24, 2004, and U.S. provisional patent application Ser. 60/590,088, filed Jul. 21, 2005, both of which are incorporated in their entirety by this reference.
  • During operation, the plates absorb energy from the applied radio frequency field as a result of conductive resistance along the surfaces of the plates. This energy appears as heat and is removed from the plates using water cooling lines 108 that release the heat in a heat exchanger 113.
  • Stray magnetic fields exiting from the cyclotron are limited by both the pillbox magnet yoke (which also serves as a shield) and a separate magnetic shield 114. The separate magnetic shield includes of a layer 117 of ferromagnetic material (e.g., steel or iron) that encloses the pillbox yoke, separated by a space 116. This configuration that includes a sandwich of a yoke, a space, and a shield achieves adequate shielding for a given leakage magnetic field at lower weight.
  • As mentioned, the gantry allows the synchrocyclotron to be rotated about the horizontal rotational axis 532. The truss structure 516 has two generally parallel spans 580, 582. The synchrocyclotron is cradled between the spans about midway between the legs. The gantry is balanced for rotation about the bearings using counterweights 122, 124 mounted on ends of the legs opposite the truss.
  • The gantry is driven to rotate by an electric motor mounted to one of the gantry legs and connected to the bearing housings by drive gears and belts or chains. The rotational position of the gantry is derived from signals provided by shaft angle encoders incorporated into the gantry drive motors and the drive gears.
  • At the location at which the ion beam exits the cyclotron, the beam formation system 125 acts on the ion beam to give it properties suitable for patient treatment. For example, the beam may be spread and its depth of penetration varied to provide uniform radiation across a given target volume. The beam formation system can include passive scattering elements as well as active scanning elements.
  • All of the active systems of the synchrocyclotron (the current driven superconducting coils, the RF-driven plates, the vacuum pumps for the vacuum acceleration chamber and for the superconducting coil cooling chamber, the current driven ion source, the hydrogen gas source, and the RF plate coolers, for example), are controlled by appropriate synchrocyclotron control electronics (not shown).
  • The control of the gantry, the patient support, the active beam shaping elements, and the synchrocyclotron to perform a therapy session is achieved by appropriate therapy control electronics (not shown).
  • As shown in FIGS. 1, 11, and 12, the gantry bearings are supported by the walls of a cyclotron vault 524. The gantry enables the cyclotron to be swung through a range 520 of 180 degrees (or more) including positions above, to the side of, and below the patient. The vault is tall enough to clear the gantry at the top and bottom extremes of its motion. A maze 146 sided by walls 148, 150 provides an entry and exit route for therapists and patients. Because at least one wall 152 is never in line with the proton beam directly from the cyclotron, it can be made relatively thin and still perform its shielding function. The other three side walls 154, 156, 150/148 of the room, which may need to be more heavily shielded, can be buried within an earthen hill (not shown). The required thickness of walls 154, 156, and 158 can be reduced, because the earth can itself provide some of the needed shielding.
  • For safety and aesthetic reasons, a therapy room 160 is constructed within the vault. The therapy room is cantilevered from walls 154, 156, 150 and the base 162 of the containing room into the space between the gantry legs in a manner that clears the swinging gantry and also maximizes the extent of the floor space 164 of the therapy room. Periodic servicing of the accelerator can be accomplished in the space below the raised floor. When the accelerator is rotated to the down position on the gantry, full access to the accelerator is possible in a space separate from the treatment area. Power supplies, cooling equipment, vacuum pumps and other support equipment can be located under the raised floor in this separate space.
  • Within the treatment room, the patient support 170 can be mounted in a variety of ways that permit the support to be raised and lowered and the patient to be rotated and moved to a variety of positions and orientations.
  • Additional information concerning the design of the accelerator can be found in U.S. provisional application Ser. No. 60/760,788, entitled HIGH-FIELD SUPERCONDUCTING SYNCHROCYCLOTRON (T. Antaya), filed Jan. 20, 2006, and U.S. patent application Ser. No. 11/463,402, entitled MAGNET STRUCTURE FOR PARTICLE ACCELERATION (T. Antaya, et al.), filed Aug. 9, 2006, and U.S. provisional application Ser. No. 60/850,565, entitled CRYOGENIC VACUUM BREAK PNEUMATIC THERMAL COUPLER (Radovinsky et al.), filed Oct. 10, 2006, all of which are incorporated in their entireties by reference here.
  • Other implementations are within the scope of the following claims.

Claims (39)

1. An apparatus comprising
a patient support, and
a gantry on which an accelerator is mounted to enable the accelerator to move through a range of positions around a patient on the patient support,
the accelerator being configured to produce a proton or ion beam having an energy level sufficient to reach an arbitrary target in the patient from positions within the range,
the proton or ion beam passing essentially directly from the accelerator housing to the patient.
2. The apparatus of claim 1 in which
the gantry is supported for rotation on two sides of the patient support.
3. The apparatus of claim 2 in which
the gantry is supported for rotation on bearings on the two sides of the patient support.
4. The apparatus of claim 1 in which the gantry comprises two arms extending from an axis of rotation of the gantry and a truss between the two arms on which the accelerator is mounted.
5. The apparatus of claim 1 in which the gantry is constrained to rotate within a range of positions that is smaller than 360 degrees.
6. The apparatus of claim 5 in which the range is at least as large as 180 degrees.
7. The apparatus of claim 5 in which the range is from about 180 degrees to about 330 degrees.
8. The apparatus of claim 5 also including radio-protective walls at least one of which is not in line with the proton or ion beam from the accelerator in any of the positions within the range, the one wall being constructed to provide the same radio-protection than the other walls with less mass.
9. The apparatus of claim 5 in which the patient support is mounted on a patient support area that is accessible through a space defined by a range of positions at which the gantry is constrained from rotation.
10. The apparatus of claim 1 in which the patient support is movable relative to the gantry.
11. The apparatus of claim 10 in which the patient support is configured for rotation about a patient axis of rotation.
12. The apparatus of claim 11 in which the patient axis of rotation is vertical.
13. The apparatus of claim 11 in which the patient axis of rotation contains an isocenter in a patient on the patient support.
14. The apparatus of claim 1 in which the patient gantry is configured for rotation of the accelerator about a gantry axis of rotation.
15. The apparatus of claim 14 in which the gantry axis of rotation is horizontal.
16. The apparatus of claim 14 in which the axis of rotation contains an isocenter in a patient on the patient support.
17. The apparatus of claim 1 in which the accelerator weighs less than 40 Tons.
18. The apparatus of claim 17 in which the accelerator weights in a range from 5 to 30 Tons.
19. The apparatus of claim 1 in which the accelerator occupies a volume of less than 4.5 cubic meters.
20. The apparatus of claim 19 in which the volume is in the range of 0.7 to 4.5 cubic meters.
21. The apparatus of claim 1 in which the accelerator produces a proton or ion beam having an energy level of at least 150 MeV.
22. The apparatus of claim 21 in which the energy level is in the range from 150 to 300 MeV.
23. The apparatus of claim 1 in which the accelerator comprising a synchrocyclotron.
24. The apparatus of claim 1 in which the accelerator comprises a magnet structure having a field strength of at least 6 Tesla.
25. The apparatus of claim 24 in which field strength is in the range of 6 to 20 Tesla.
26. The apparatus of claim 24 in which the magnet structure comprises superconducting windings.
27. The apparatus of claim 1 in which the proton or ion beam passes directly from the accelerator to the general area of the patient stand.
28. The apparatus of claim 1 also including a shielding chamber containing the patient support, the gantry, and the accelerator, at least one wall of the chamber being thinner than other walls of the chamber.
29. The apparatus of claim 28 in which at least a portion of the chamber is embedded within the earth.
30. An apparatus comprising
a patient support, and
a gantry on which an accelerator is mounted, the gantry being supported on two sides of the patient support for rotation (a) about a horizontal gantry axis that contains an isocenter in the patient and (b) through a range of positions that is smaller than 360 degrees,
the patient support being rotatable about a vertical patient support axis that contains the isocenter,
the accelerator comprising a synchrocyclotron configured to produce a proton or ion beam having an energy level of at least 150 MeV to reach any arbitrary target in the patient directly from positions within the range, the synchrocyclotron having superconducting windings.
31. A method comprising
supporting a patient within a treatment space,
causing a beam of proton or ions to pass in a straight line direction from an output of an accelerator to any arbitrary target within the patient, and
causing the straight line direction to be varied through a range of directions around the patient.
32. An apparatus comprising
an accelerator configured to produce a particle beam and to be mounted on a gantry that enables the accelerator to move through any range of positions around a patient on a patient support,
the accelerator being configured to produce a particle beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range.
33. An apparatus comprising
a gantry configured to hold an accelerator and to enable the accelerator to move through a range of positions around a patient on a patient support,
the accelerator being configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range.
34. A structure comprising
a patient support,
a gantry on which an accelerator is mounted to enable the accelerator to move through a range of positions around a patient on the patient support,
the accelerator being configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in the patient from positions within the range, and
a walled enclosure containing the patient support, the gantry, and the accelerator.
35. An apparatus comprising
an accelerator configured to produce a proton or ion beam having an energy level sufficient to reach any arbitrary target in a patient, the accelerator being small enough and lightweight enough to be mounted on a rotatable gantry in an orientation to permit the proton or ion beam to pass essentially directly from the accelerator to the patient.
36. An apparatus comprising
a medical synchrocyclotron having a superconducting electromagnetic structure that generates a field strength of at least 6 Tesla, produces a beam of particles having an energy level of at least 150 MeV, has a volume no larger than 4.5 cubic meters, and has a weight less than 30 Tons.
37. The apparatus of claim 35 in which the accelerator comprises a superconducting synchrocyclotron.
38. The apparatus of claim 37 in which the magnetic field of the superconducting synchrocyclotron is in the range of 6 to 20 Tesla.
39. The apparatus of claim 34 in which more than half of the surface of the walled enclosure is embedded within the earth.
US12/618,297 2005-11-18 2009-11-13 Charged particle radiation therapy Abandoned US20100230617A1 (en)

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US11/601,056 US7728311B2 (en) 2005-11-18 2006-11-17 Charged particle radiation therapy
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US12/618,297 Abandoned US20100230617A1 (en) 2005-11-18 2009-11-13 Charged particle radiation therapy
US13/303,110 Expired - Fee Related US8907311B2 (en) 2005-11-18 2011-11-22 Charged particle radiation therapy
US13/532,530 Expired - Fee Related US8916843B2 (en) 2005-11-18 2012-06-25 Inner gantry
US14/542,966 Expired - Fee Related US9452301B2 (en) 2005-11-18 2014-11-17 Inner gantry
US15/221,855 Expired - Fee Related US9925395B2 (en) 2005-11-18 2016-07-28 Inner gantry
US15/266,372 Abandoned US20170001040A1 (en) 2005-11-18 2016-09-15 Inner gantry
US15/896,458 Active US10279199B2 (en) 2005-11-18 2018-02-14 Inner gantry
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US14/542,966 Expired - Fee Related US9452301B2 (en) 2005-11-18 2014-11-17 Inner gantry
US15/221,855 Expired - Fee Related US9925395B2 (en) 2005-11-18 2016-07-28 Inner gantry
US15/266,372 Abandoned US20170001040A1 (en) 2005-11-18 2016-09-15 Inner gantry
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US16/251,253 Active US10722735B2 (en) 2005-11-18 2019-01-18 Inner gantry

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Publication number Priority date Publication date Assignee Title
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US8378321B2 (en) 2008-05-22 2013-02-19 Vladimir Balakin Charged particle cancer therapy and patient positioning method and apparatus
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US20130184512A1 (en) * 2010-07-28 2013-07-18 Sumitomo Heavy Industries, Ltd. Charged particle beam irradiation device
US8519365B2 (en) 2008-05-22 2013-08-27 Vladimir Balakin Charged particle cancer therapy imaging method and apparatus
US8569717B2 (en) 2008-05-22 2013-10-29 Vladimir Balakin Intensity modulated three-dimensional radiation scanning method and apparatus
US8581523B2 (en) 2007-11-30 2013-11-12 Mevion Medical Systems, Inc. Interrupted particle source
US8598543B2 (en) 2008-05-22 2013-12-03 Vladimir Balakin Multi-axis/multi-field charged particle cancer therapy method and apparatus
US8625739B2 (en) 2008-07-14 2014-01-07 Vladimir Balakin Charged particle cancer therapy x-ray method and apparatus
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US8627822B2 (en) 2008-07-14 2014-01-14 Vladimir Balakin Semi-vertical positioning method and apparatus used in conjunction with a charged particle cancer therapy system
US8637833B2 (en) 2008-05-22 2014-01-28 Vladimir Balakin Synchrotron power supply apparatus and method of use thereof
WO2014018876A1 (en) 2012-07-27 2014-01-30 Massachusetts Institute Of Technology Ultra-light, magnetically shielded, high-current, compact cyclotron
US8688197B2 (en) 2008-05-22 2014-04-01 Vladimir Yegorovich Balakin Charged particle cancer therapy patient positioning method and apparatus
US20140094640A1 (en) * 2012-09-28 2014-04-03 Mevion Medical Systems, Inc. Magnetic Field Regenerator
US8718231B2 (en) 2008-05-22 2014-05-06 Vladimir Balakin X-ray tomography method and apparatus used in conjunction with a charged particle cancer therapy system
US8766217B2 (en) 2008-05-22 2014-07-01 Vladimir Yegorovich Balakin Multi-field charged particle cancer therapy method and apparatus
US8791435B2 (en) 2009-03-04 2014-07-29 Vladimir Egorovich Balakin Multi-field charged particle cancer therapy method and apparatus
US8791656B1 (en) 2013-05-31 2014-07-29 Mevion Medical Systems, Inc. Active return system
US20140257099A1 (en) * 2008-05-22 2014-09-11 Vladimir Balakin Treatment delivery control system and method of operation thereof
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US8901509B2 (en) 2008-05-22 2014-12-02 Vladimir Yegorovich Balakin Multi-axis charged particle cancer therapy method and apparatus
US8907309B2 (en) 2009-04-17 2014-12-09 Stephen L. Spotts Treatment delivery control system and method of operation thereof
US8933651B2 (en) 2012-11-16 2015-01-13 Vladimir Balakin Charged particle accelerator magnet apparatus and method of use thereof
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US9155186B2 (en) 2012-09-28 2015-10-06 Mevion Medical Systems, Inc. Focusing a particle beam using magnetic field flutter
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US9452301B2 (en) 2005-11-18 2016-09-27 Mevion Medical Systems, Inc. Inner gantry
US9498649B2 (en) 2008-05-22 2016-11-22 Vladimir Balakin Charged particle cancer therapy patient constraint apparatus and method of use thereof
US20160339272A1 (en) * 2008-05-22 2016-11-24 W. Davis Lee Ion beam extraction apparatus and method of use thereof
US9545528B2 (en) 2012-09-28 2017-01-17 Mevion Medical Systems, Inc. Controlling particle therapy
US9579525B2 (en) 2008-05-22 2017-02-28 Vladimir Balakin Multi-axis charged particle cancer therapy method and apparatus
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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
US9682254B2 (en) 2008-05-22 2017-06-20 Vladimir Balakin Cancer surface searing apparatus and method of use thereof
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
US9737733B2 (en) 2008-05-22 2017-08-22 W. Davis Lee Charged particle state determination apparatus and method of use thereof
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US9744380B2 (en) 2008-05-22 2017-08-29 Susan L. Michaud Patient specific beam control assembly of a cancer therapy apparatus and method of use thereof
US9782140B2 (en) 2008-05-22 2017-10-10 Susan L. Michaud Hybrid charged particle / X-ray-imaging / treatment apparatus and method of use thereof
US9855444B2 (en) 2008-05-22 2018-01-02 Scott Penfold X-ray detector for proton transit detection apparatus and method of use thereof
US9910166B2 (en) 2008-05-22 2018-03-06 Stephen L. Spotts Redundant charged particle state determination apparatus and method of use thereof
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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
US9974978B2 (en) 2008-05-22 2018-05-22 W. Davis Lee Scintillation array apparatus and method of use thereof
US10029122B2 (en) 2008-05-22 2018-07-24 Susan L. Michaud Charged particle—patient motion control system apparatus and method of use thereof
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US10037863B2 (en) 2016-05-27 2018-07-31 Mark R. Amato Continuous ion beam kinetic energy dissipater apparatus and method of use thereof
US10070831B2 (en) 2008-05-22 2018-09-11 James P. Bennett Integrated cancer therapy—imaging apparatus and method of use thereof
US10086214B2 (en) 2010-04-16 2018-10-02 Vladimir Balakin Integrated tomography—cancer treatment apparatus and method of use thereof
US10092776B2 (en) 2008-05-22 2018-10-09 Susan L. Michaud Integrated translation/rotation charged particle imaging/treatment apparatus and method of use thereof
US10143854B2 (en) 2008-05-22 2018-12-04 Susan L. Michaud Dual rotation charged particle imaging / treatment apparatus and method of use thereof
US10179250B2 (en) 2010-04-16 2019-01-15 Nick Ruebel Auto-updated and implemented radiation treatment plan apparatus and method of use thereof
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
US10349906B2 (en) 2010-04-16 2019-07-16 James P. Bennett Multiplexed proton tomography imaging apparatus and method of use thereof
US10376717B2 (en) 2010-04-16 2019-08-13 James P. Bennett Intervening object compensating automated radiation treatment plan development apparatus and method of use thereof
US10518109B2 (en) 2010-04-16 2019-12-31 Jillian Reno Transformable charged particle beam path cancer therapy apparatus and method of use thereof
US10548551B2 (en) 2008-05-22 2020-02-04 W. Davis Lee Depth resolved scintillation detector array imaging apparatus and method of use thereof
US10555710B2 (en) 2010-04-16 2020-02-11 James P. Bennett Simultaneous multi-axes imaging apparatus and method of use thereof
US10556126B2 (en) 2010-04-16 2020-02-11 Mark R. Amato Automated radiation treatment plan development apparatus and method of use thereof
US10589128B2 (en) 2010-04-16 2020-03-17 Susan L. Michaud Treatment beam path verification in a cancer therapy apparatus and method of use thereof
US10625097B2 (en) 2010-04-16 2020-04-21 Jillian Reno Semi-automated cancer therapy treatment apparatus and method of use thereof
US10638988B2 (en) 2010-04-16 2020-05-05 Scott Penfold Simultaneous/single patient position X-ray and proton imaging apparatus and method of use thereof
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
USRE48047E1 (en) 2004-07-21 2020-06-09 Mevion Medical Systems, Inc. Programmable radio frequency waveform generator for a synchrocyclotron
US10684380B2 (en) 2008-05-22 2020-06-16 W. Davis Lee Multiple scintillation detector array imaging apparatus and method of use thereof
US10751551B2 (en) 2010-04-16 2020-08-25 James P. Bennett Integrated imaging-cancer treatment apparatus and method of use thereof
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
US11648420B2 (en) 2010-04-16 2023-05-16 Vladimir Balakin Imaging assisted integrated tomography—cancer treatment apparatus and method of use thereof

Families Citing this family (68)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005081842A2 (en) 2004-02-20 2005-09-09 University Of Florida Research Foundation, Inc. System for delivering conformal radiation therapy while simultaneously imaging soft tissue
US7656258B1 (en) 2006-01-19 2010-02-02 Massachusetts Institute Of Technology Magnet structure for particle acceleration
EP1977632A2 (en) * 2006-01-19 2008-10-08 Massachusetts Institute Of Technology High-field superconducting synchrocyclotron
DE202006019307U1 (en) * 2006-12-21 2008-04-24 Accel Instruments Gmbh irradiator
JP4228018B2 (en) * 2007-02-16 2009-02-25 三菱重工業株式会社 Medical equipment
US8093568B2 (en) * 2007-02-27 2012-01-10 Wisconsin Alumni Research Foundation Ion radiation therapy system with rocking gantry motion
US20090154645A1 (en) * 2007-05-24 2009-06-18 Leon Lifshitz Teletherapy treatment center
DE102007032025A1 (en) * 2007-07-10 2008-12-18 Siemens Ag Particle therapy installation for treating patients with cancer comprises a cylindrical gantry rotating about a rotary axis with a rotating beam generator and a beam channel for guiding the particle beam produced
DE102007033894B3 (en) * 2007-07-20 2008-12-11 Siemens Ag Particle beam application device, irradiation device and method for guiding a particle beam
US8003964B2 (en) * 2007-10-11 2011-08-23 Still River Systems Incorporated Applying a particle beam to a patient
WO2009051697A1 (en) * 2007-10-12 2009-04-23 Varian Medical Systems, Inc. Charged particle accelerators, radiation sources, systems, and methods
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
ES2547342T3 (en) * 2007-11-30 2015-10-05 Mevion Medical Systems, Inc. Interior porch
US20090314960A1 (en) * 2008-05-22 2009-12-24 Vladimir Balakin Patient positioning method and apparatus used in conjunction with a charged particle cancer therapy system
US8394007B2 (en) * 2008-10-31 2013-03-12 Toby D Henderson Inclined beamline motion mechanism
DE102009007370A1 (en) * 2009-02-04 2010-08-12 Siemens Aktiengesellschaft Method for operating a radiotherapy device
GB2467595B (en) 2009-02-09 2011-08-24 Tesla Engineering Ltd Cooling systems and methods
US8053745B2 (en) * 2009-02-24 2011-11-08 Moore John F Device and method for administering particle beam therapy
US8153997B2 (en) * 2009-05-05 2012-04-10 General Electric Company Isotope production system and cyclotron
US8106570B2 (en) * 2009-05-05 2012-01-31 General Electric Company Isotope production system and cyclotron having reduced magnetic stray fields
US8106370B2 (en) * 2009-05-05 2012-01-31 General Electric Company Isotope production system and cyclotron having a magnet yoke with a pump acceptance cavity
EP2446718B1 (en) 2009-06-24 2018-03-28 Ion Beam Applications S.A. Device for particle beam production
US8374306B2 (en) * 2009-06-26 2013-02-12 General Electric Company Isotope production system with separated shielding
WO2011008969A1 (en) 2009-07-15 2011-01-20 Viewray Incorporated Method and apparatus for shielding a linear accelerator and a magnetic resonance imaging device from each other
DK2308561T3 (en) * 2009-09-28 2011-10-03 Ion Beam Applic Compact gantry for particle therapy
KR101284171B1 (en) * 2009-12-18 2013-07-10 한국전자통신연구원 Treatment Apparatus Using Proton and Method of Treating Using the Same
US20110224475A1 (en) * 2010-02-12 2011-09-15 Andries Nicolaas Schreuder Robotic mobile anesthesia system
US9693443B2 (en) 2010-04-19 2017-06-27 General Electric Company Self-shielding target for isotope production systems
US8755489B2 (en) 2010-11-11 2014-06-17 P-Cure, Ltd. Teletherapy location and dose distribution control system and method
US8653762B2 (en) * 2010-12-23 2014-02-18 General Electric Company Particle accelerators having electromechanical motors and methods of operating and manufacturing the same
JP5744578B2 (en) 2011-03-10 2015-07-08 住友重機械工業株式会社 Charged particle beam irradiation system and neutron beam irradiation system
US8981779B2 (en) 2011-12-13 2015-03-17 Viewray Incorporated Active resistive shimming fro MRI devices
US10561861B2 (en) 2012-05-02 2020-02-18 Viewray Technologies, Inc. Videographic display of real-time medical treatment
JP6121544B2 (en) * 2012-09-28 2017-04-26 メビオン・メディカル・システムズ・インコーポレーテッド Particle beam focusing
EP2911745B1 (en) 2012-10-26 2019-08-07 ViewRay Technologies, Inc. Assessment and improvement of treatment using imaging of physiological responses to radiation therapy
JP6138466B2 (en) * 2012-12-03 2017-05-31 住友重機械工業株式会社 cyclotron
JP5662502B2 (en) * 2013-03-07 2015-01-28 メビオン・メディカル・システムズ・インコーポレーテッド Inner gantry
JP5662503B2 (en) * 2013-03-07 2015-01-28 メビオン・メディカル・システムズ・インコーポレーテッド Inner gantry
US9446263B2 (en) 2013-03-15 2016-09-20 Viewray Technologies, Inc. Systems and methods for linear accelerator radiotherapy with magnetic resonance imaging
CN103228093A (en) * 2013-04-20 2013-07-31 胡明建 Design method of superconductor focusing synchrocyclotron
CN105792892A (en) * 2013-09-20 2016-07-20 普罗诺瓦解决方案有限责任公司 Treatment theater system for proton therapy
WO2015070865A1 (en) * 2013-11-14 2015-05-21 Danfysik A/S Particle therapy system
DE102014003536A1 (en) * 2014-03-13 2015-09-17 Forschungszentrum Jülich GmbH Fachbereich Patente Superconducting magnetic field stabilizer
WO2015161036A1 (en) * 2014-04-16 2015-10-22 The Board Of Regents Of The University Of Texas System Radiation therapy systems that include primary radiation shielding, and modular secondary radiation shields
WO2016051550A1 (en) * 2014-10-01 2016-04-07 株式会社日立製作所 Particle beam therapy apparatus, and operation method therefor
EP3232742B1 (en) * 2014-12-08 2020-11-18 Hitachi, Ltd. Accelerator and particle beam radiation device
JP6085070B1 (en) * 2015-04-09 2017-02-22 三菱電機株式会社 Treatment planning device and particle beam treatment device
KR20180120705A (en) 2016-03-02 2018-11-06 뷰레이 테크놀로지스 인크. Particle therapy using magnetic resonance imaging
US20170348547A1 (en) * 2016-05-27 2017-12-07 W. Davis Lee Ion beam kinetic energy dissipater apparatus and method of use thereof
AU2017281519A1 (en) 2016-06-22 2019-01-24 Viewray Technologies, Inc. Magnetic resonance imaging at low field strength
US20180122544A1 (en) 2016-11-03 2018-05-03 Mevion Medical Systems, Inc. Superconducting coil configuration
CN110382049A (en) 2016-12-13 2019-10-25 优瑞技术公司 Radiotherapy system and method
US10617886B2 (en) * 2016-12-22 2020-04-14 Hitachi, Ltd. Accelerator and particle therapy system
JP6529524B2 (en) * 2017-01-05 2019-06-12 住友重機械工業株式会社 Particle therapy equipment
US10603518B2 (en) * 2017-03-14 2020-03-31 Varian Medical Systems, Inc. Rotatable cantilever gantry in radiotherapy system
JP2020515016A (en) 2017-03-24 2020-05-21 メビオン・メディカル・システムズ・インコーポレーテッド Coil positioning system
JP6739393B2 (en) * 2017-04-18 2020-08-12 株式会社日立製作所 Particle beam accelerator and particle beam therapy system
US10984935B2 (en) * 2017-05-02 2021-04-20 Hefei Institutes Of Physical Science, Chinese Academy Of Sciences Superconducting dipole magnet structure for particle deflection
US10039935B1 (en) * 2017-10-11 2018-08-07 HIL Applied Medical, Ltd. Systems and methods for providing an ion beam
US11033758B2 (en) 2017-12-06 2021-06-15 Viewray Technologies, Inc. Radiotherapy systems, methods and software
US11209509B2 (en) 2018-05-16 2021-12-28 Viewray Technologies, Inc. Resistive electromagnet systems and methods
NL2021421B1 (en) 2018-08-03 2020-02-12 Itrec Bv Proton Therapy Gantry
CN109224321B (en) * 2018-10-29 2019-08-02 合肥中科离子医学技术装备有限公司 A kind of proton heavy particle therapy system based on synchrocyclotron
MX2021007106A (en) 2018-12-14 2022-09-05 Rad Tech Medical Systems Llc Shielding facility and method of making thereof.
CN113474040A (en) 2019-01-10 2021-10-01 普罗诺瓦解决方案有限责任公司 Compact proton therapy system and method
GB2583140B (en) * 2019-04-18 2023-08-30 Muir Ip Ltd Radiation therapy system
JP7352412B2 (en) * 2019-08-28 2023-09-28 住友重機械工業株式会社 cyclotron
CN116421899A (en) * 2023-04-28 2023-07-14 杭州嘉辐科技有限公司 Superconductive heavy ion rotary frame

Citations (90)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2280606A (en) * 1940-01-26 1942-04-21 Rca Corp Electronic reactance circuits
US3582650A (en) * 1960-08-01 1971-06-01 Varian Associates Support structure for electron accelerator with deflecting means and target and cooperating patient support
US3757118A (en) * 1972-02-22 1973-09-04 Ca Atomic Energy Ltd Electron beam therapy unit
US3886367A (en) * 1974-01-18 1975-05-27 Us Energy Ion-beam mask for cancer patient therapy
US3955089A (en) * 1974-10-21 1976-05-04 Varian Associates Automatic steering of a high velocity beam of charged particles
US4112306A (en) * 1976-12-06 1978-09-05 Varian Associates, Inc. Neutron irradiation therapy machine
US4139777A (en) * 1975-11-19 1979-02-13 Rautenbach Willem L Cyclotron and neutron therapy installation incorporating such a cyclotron
US4197510A (en) * 1978-06-23 1980-04-08 The United States Of America As Represented By The Secretary Of The Navy Isochronous cyclotron
US4220866A (en) * 1977-12-30 1980-09-02 Siemens Aktiengesellschaft Electron applicator
US4256966A (en) * 1979-07-03 1981-03-17 Siemens Medical Laboratories, Inc. Radiotherapy apparatus with two light beam localizers
US4336505A (en) * 1980-07-14 1982-06-22 John Fluke Mfg. Co., Inc. Controlled frequency signal source apparatus including a feedback path for the reduction of phase noise
US4345210A (en) * 1979-05-31 1982-08-17 C.G.R. Mev Microwave resonant system with dual resonant frequency and a cyclotron fitted with such a system
US4425506A (en) * 1981-11-19 1984-01-10 Varian Associates, Inc. Stepped gap achromatic bending magnet
US4507614A (en) * 1983-03-21 1985-03-26 The United States Of America As Represented By The United States Department Of Energy Electrostatic wire for stabilizing a charged particle beam
US4507616A (en) * 1982-03-08 1985-03-26 Board Of Trustees Operating Michigan State University Rotatable superconducting cyclotron adapted for medical use
US4589126A (en) * 1984-01-26 1986-05-13 Augustsson Nils E Radiotherapy treatment table
US4598208A (en) * 1982-10-04 1986-07-01 Varian Associates, Inc. Collimation system for electron arc therapy
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
US4651007A (en) * 1984-09-13 1987-03-17 Technicare Corporation Medical diagnostic mechanical positioner
US4680565A (en) * 1985-06-24 1987-07-14 Siemens Aktiengesellschaft Magnetic field device for a system for the acceleration and/or storage of electrically charged particles
US4726046A (en) * 1985-11-05 1988-02-16 Varian Associates, Inc. X-ray and electron radiotherapy clinical treatment machine
US4734653A (en) * 1985-02-25 1988-03-29 Siemens Aktiengesellschaft Magnetic field apparatus for a particle accelerator having a supplemental winding with a hollow groove structure
US4736173A (en) * 1983-06-30 1988-04-05 Hughes Aircraft Company Thermally-compensated microwave resonator utilizing current-null segmentation
US4737727A (en) * 1986-02-12 1988-04-12 Mitsubishi Denki Kabushiki Kaisha Charged beam apparatus
US4745367A (en) * 1985-03-28 1988-05-17 Kernforschungszentrum Karlsruhe Gmbh Superconducting magnet system for particle accelerators of a synchrotron radiation source
US4754147A (en) * 1986-04-11 1988-06-28 Michigan State University Variable radiation collimator
US4769623A (en) * 1987-01-28 1988-09-06 Siemens Aktiengesellschaft Magnetic device with curved superconducting coil windings
US4771208A (en) * 1985-05-10 1988-09-13 Yves Jongen Cyclotron
US4808941A (en) * 1986-10-29 1989-02-28 Siemens Aktiengesellschaft Synchrotron with radiation absorber
US4812658A (en) * 1987-07-23 1989-03-14 President And Fellows Of Harvard College Beam Redirecting
US4843333A (en) * 1987-01-28 1989-06-27 Siemens Aktiengesellschaft Synchrotron radiation source having adjustable fixed curved coil windings
US4865284A (en) * 1984-03-13 1989-09-12 Siemens Gammasonics, Inc. Collimator storage device in particular a collimator cart
US4868844A (en) * 1986-09-10 1989-09-19 Varian Associates, Inc. Mutileaf collimator for radiotherapy machines
US4902993A (en) * 1987-02-19 1990-02-20 Kernforschungszentrum Karlsruhe Gmbh Magnetic deflection system for charged particles
US4905267A (en) * 1988-04-29 1990-02-27 Loma Linda University Medical Center Method of assembly and whole body, patient positioning and repositioning support for use in radiation beam therapy systems
US4904949A (en) * 1984-08-28 1990-02-27 Oxford Instruments Limited Synchrotron with superconducting coils and arrangement thereof
US4917344A (en) * 1988-04-07 1990-04-17 Loma Linda University Medical Center Roller-supported, modular, isocentric gantry and method of assembly
US4943781A (en) * 1985-05-21 1990-07-24 Oxford Instruments, Ltd. Cyclotron with yokeless superconducting magnet
US4987309A (en) * 1988-11-29 1991-01-22 Varian Associates, Inc. Radiation therapy unit
US4996496A (en) * 1987-09-11 1991-02-26 Hitachi, Ltd. Bending magnet
US5017882A (en) * 1988-09-01 1991-05-21 Amersham International Plc Proton source
US5017789A (en) * 1989-03-31 1991-05-21 Loma Linda University Medical Center Raster scan control system for a charged-particle beam
US5036290A (en) * 1989-03-15 1991-07-30 Hitachi, Ltd. Synchrotron radiation generation apparatus
US5039867A (en) * 1987-08-24 1991-08-13 Mitsubishi Denki Kabushiki Kaisha Therapeutic apparatus
US5111173A (en) * 1990-03-27 1992-05-05 Mitsubishi Denki Kabushiki Kaisha Deflection electromagnet for a charged particle device
US5117194A (en) * 1988-08-26 1992-05-26 Mitsubishi Denki Kabushiki Kaisha Device for accelerating and storing charged particles
US5117212A (en) * 1989-01-12 1992-05-26 Mitsubishi Denki Kabushiki Kaisha Electromagnet for charged-particle apparatus
US5117829A (en) * 1989-03-31 1992-06-02 Loma Linda University Medical Center Patient alignment system and procedure for radiation treatment
US5189687A (en) * 1987-12-03 1993-02-23 University Of Florida Research Foundation, Inc. Apparatus for stereotactic radiosurgery
US5240218A (en) * 1991-10-23 1993-08-31 Loma Linda University Medical Center Retractable support assembly
US5278533A (en) * 1990-08-31 1994-01-11 Mitsubishi Denki Kabushiki Kaisha Coil for use in charged particle deflecting electromagnet and method of manufacturing the same
US5317164A (en) * 1991-06-12 1994-05-31 Mitsubishi Denki Kabushiki Kaisha Radiotherapy device
US5336891A (en) * 1992-06-16 1994-08-09 Arch Development Corporation Aberration free lens system for electron microscope
US5341104A (en) * 1990-08-06 1994-08-23 Siemens Aktiengesellschaft Synchrotron radiation source
US5382914A (en) * 1992-05-05 1995-01-17 Accsys Technology, Inc. Proton-beam therapy linac
US5401973A (en) * 1992-12-04 1995-03-28 Atomic Energy Of Canada Limited Industrial material processing electron linear accelerator
US5405235A (en) * 1991-07-26 1995-04-11 Lebre; Charles J. P. Barrel grasping device for automatically clamping onto the pole of a barrel trolley
US5440133A (en) * 1993-07-02 1995-08-08 Loma Linda University Medical Center Charged particle beam scattering system
US5511549A (en) * 1995-02-13 1996-04-30 Loma Linda Medical Center Normalizing and calibrating therapeutic radiation delivery systems
US5521469A (en) * 1991-11-22 1996-05-28 Laisne; Andre E. P. Compact isochronal cyclotron
US5726448A (en) * 1996-08-09 1998-03-10 California Institute Of Technology Rotating field mass and velocity analyzer
US5751781A (en) * 1995-10-07 1998-05-12 Elekta Ab Apparatus for treating a patient
US5778047A (en) * 1996-10-24 1998-07-07 Varian Associates, Inc. Radiotherapy couch top
US6407505B1 (en) * 2001-02-01 2002-06-18 Siemens Medical Solutions Usa, Inc. Variable energy linear accelerator
US6519316B1 (en) * 2001-11-02 2003-02-11 Siemens Medical Solutions Usa, Inc.. Integrated control of portal imaging device
US20030125622A1 (en) * 1999-03-16 2003-07-03 Achim Schweikard Apparatus and method for compensating for respiratory and patient motion during treatment
US20030136924A1 (en) * 2000-06-30 2003-07-24 Gerhard Kraft Device for irradiating a tumor tissue
US6600164B1 (en) * 1999-02-19 2003-07-29 Gesellschaft Fuer Schwerionenforschung Mbh Method of operating an ion beam therapy system with monitoring of beam position
US6683318B1 (en) * 1998-09-11 2004-01-27 Gesellschaft Fuer Schwerionenforschung Mbh Ion beam therapy system and a method for operating the system
US20040017888A1 (en) * 2002-07-24 2004-01-29 Seppi Edward J. Radiation scanning of objects for contraband
US6736831B1 (en) * 1999-02-19 2004-05-18 Gesellschaft Fuer Schwerionenforschung Mbh Method for operating an ion beam therapy system by monitoring the distribution of the radiation dose
US6745072B1 (en) * 1999-02-19 2004-06-01 Gesellschaft Fuer Schwerionenforschung Mbh Method for checking beam generation and beam acceleration means of an ion beam therapy system
US6777689B2 (en) * 2001-11-16 2004-08-17 Ion Beam Application, S.A. Article irradiation system shielding
US20040159795A1 (en) * 2002-09-05 2004-08-19 Man Technologie Ag Isokinetic gantry arrangement for the isocentric guidance of a particle beam and a method for constructing same
US6853703B2 (en) * 2001-07-20 2005-02-08 Siemens Medical Solutions Usa, Inc. Automated delivery of treatment fields
US6865254B2 (en) * 2002-07-02 2005-03-08 Pencilbeam Technologies Ab Radiation system with inner and outer gantry parts
US20050058245A1 (en) * 2003-09-11 2005-03-17 Moshe Ein-Gal Intensity-modulated radiation therapy with a multilayer multileaf collimator
US6984835B2 (en) * 2003-04-23 2006-01-10 Mitsubishi Denki Kabushiki Kaisha Irradiation apparatus and irradiation method
US20060017015A1 (en) * 2004-07-21 2006-01-26 Still River Systems, Inc. Programmable particle scatterer for radiation therapy beam formation
US6993112B2 (en) * 2002-03-12 2006-01-31 Deutsches Krebsforschungszentrum Stiftung Des Oeffentlichen Rechts Device for performing and verifying a therapeutic treatment and corresponding computer program and control method
US7008105B2 (en) * 2002-05-13 2006-03-07 Siemens Aktiengesellschaft Patient support device for radiation therapy
US20060067468A1 (en) * 2004-09-30 2006-03-30 Eike Rietzel Radiotherapy systems
US20060145088A1 (en) * 2003-06-02 2006-07-06 Fox Chase Cancer Center High energy polyenergetic ion selection systems, ion beam therapy systems, and ion beam treatment centers
US20070029510A1 (en) * 2005-08-05 2007-02-08 Siemens Aktiengesellschaft Gantry system for a particle therapy facility
US20070051904A1 (en) * 2005-08-30 2007-03-08 Werner Kaiser Gantry system for particle therapy, therapy plan or radiation method for particle therapy with such a gantry system
US7208745B2 (en) * 2005-08-18 2007-04-24 Konica Minolta Medical & Graphic, Inc. Radiation image conversion panel
US20070171015A1 (en) * 2006-01-19 2007-07-26 Massachusetts Institute Of Technology High-Field Superconducting Synchrocyclotron
US7348579B2 (en) * 2002-09-18 2008-03-25 Paul Scherrer Institut Arrangement for performing proton therapy
US7656258B1 (en) * 2006-01-19 2010-02-02 Massachusetts Institute Of Technology Magnet structure for particle acceleration

Family Cites Families (544)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US774018A (en) 1901-07-29 1904-11-01 Caspar Wuest-Kunz Alternating-current motor.
US2615129A (en) 1947-05-16 1952-10-21 Edwin M Mcmillan Synchro-cyclotron
US2492324A (en) 1947-12-24 1949-12-27 Collins Radio Co Cyclotron oscillator system
US2659000A (en) 1951-04-27 1953-11-10 Collins Radio Co Variable frequency cyclotron
US2789222A (en) 1954-07-21 1957-04-16 Marvin D Martin Frequency modulation system
US2958327A (en) 1957-03-29 1960-11-01 Gladys W Geissmann Foundation garment
GB957342A (en) * 1960-08-01 1964-05-06 Varian Associates Apparatus for directing ionising radiation in the form of or produced by beams from particle accelerators
US3175131A (en) 1961-02-08 1965-03-23 Richard J Burleigh Magnet construction for a variable energy cyclotron
US3432721A (en) 1966-01-17 1969-03-11 Gen Electric Beam plasma high frequency wave generating system
US3358463A (en) 1966-07-15 1967-12-19 Lockheed Aircraft Corp Integrated superconducting magnetcryostat system
JPS4323267Y1 (en) 1966-10-11 1968-10-01
JPS4728762Y1 (en) 1967-04-21 1972-08-30
NL7007871A (en) 1970-05-29 1971-12-01
US3679899A (en) 1971-04-16 1972-07-25 Nasa Nondispersive gas analyzing method and apparatus wherein radiation is serially passed through a reference and unknown gas
JPS4728762U (en) 1971-04-23 1972-12-01
JPS5036158Y2 (en) 1972-03-09 1975-10-21
US3867635A (en) * 1973-01-22 1975-02-18 Varian Associates Achromatic magnetic beam deflection system
US3944679A (en) 1973-04-13 1976-03-16 The Japan Tobacco & Salt Public Corporation Process for imparting a coumarin-like aroma and flavor to tobacco, foods and drinks
CA966893A (en) 1973-06-19 1975-04-29 Her Majesty In Right Of Canada As Represented By Atomic Energy Of Canada Limited Superconducting cyclotron
US4047068A (en) 1973-11-26 1977-09-06 Kreidl Chemico Physical K.G. Synchronous plasma packet accelerator
US3992625A (en) 1973-12-27 1976-11-16 Jersey Nuclear-Avco Isotopes, Inc. Method and apparatus for extracting ions from a partially ionized plasma using a magnetic field gradient
US3958327A (en) 1974-05-01 1976-05-25 Airco, Inc. Stabilized high-field superconductor
US4129784A (en) 1974-06-14 1978-12-12 Siemens Aktiengesellschaft Gamma camera
US3925676A (en) 1974-07-31 1975-12-09 Ca Atomic Energy Ltd Superconducting cyclotron neutron source for therapy
US4230129A (en) 1975-07-11 1980-10-28 Leveen Harry H Radio frequency, electromagnetic radiation device having orbital mount
SU569635A1 (en) 1976-03-01 1977-08-25 Предприятие П/Я М-5649 Magnetic alloy
US4038622A (en) 1976-04-13 1977-07-26 The United States Of America As Represented By The United States Energy Research And Development Administration Superconducting dipole electromagnet
GB2015821B (en) 1978-02-28 1982-03-31 Radiation Dynamics Ltd Racetrack linear accelerators
JPS5924520B2 (en) 1979-03-07 1984-06-09 理化学研究所 Structure of the magnetic pole of an isochronous cyclotron and how to use it
US4239772A (en) 1979-05-30 1980-12-16 International Minerals & Chemical Corp. Allyl and propyl zearalenone derivatives and their use as growth promoting agents
US4293772A (en) 1980-03-31 1981-10-06 Siemens Medical Laboratories, Inc. Wobbling device for a charged particle accelerator
US4342060A (en) 1980-05-22 1982-07-27 Siemens Medical Laboratories, Inc. Energy interlock system for a linear accelerator
JPS57162527A (en) 1981-03-31 1982-10-06 Fujitsu Ltd Setting device for preset voltage of frequency synthesizer
JPS57162527U (en) 1981-04-07 1982-10-13
DE3148100A1 (en) 1981-12-04 1983-06-09 Uwe Hanno Dr. 8050 Freising Trinks Synchrotron X-ray radiation source
JPS58107060A (en) 1981-12-18 1983-06-25 Fuji Electric Co Ltd Superconducting rotor provided with emergency pressure releasing device
JPS58141000A (en) 1982-02-16 1983-08-20 住友重機械工業株式会社 Cyclotron
JPS58141000U (en) 1982-03-15 1983-09-22 和泉鉄工株式会社 Vertical reversal loading/unloading device
US4490616A (en) 1982-09-30 1984-12-25 Cipollina John J Cephalometric shield
JPS59208795A (en) 1983-05-12 1984-11-27 Toshiba Corp Cryogenic device
JPS6030971U (en) 1983-08-08 1985-03-02 カルソニックカンセイ株式会社 Deformed tube evaporator
JPS6076717A (en) 1983-10-03 1985-05-01 Olympus Optical Co Ltd Endoscope device
DE3344046A1 (en) 1983-12-06 1985-06-20 Brown, Boveri & Cie Ag, 6800 Mannheim COOLING SYSTEM FOR INDIRECTLY COOLED SUPRALINE MAGNETS
FR2560421B1 (en) 1984-02-28 1988-06-17 Commissariat Energie Atomique DEVICE FOR COOLING SUPERCONDUCTING WINDINGS
JPS6180800U (en) 1984-10-30 1986-05-29
EP0193837B1 (en) 1985-03-08 1990-05-02 Siemens Aktiengesellschaft Magnetic field-generating device for a particle-accelerating system
NL8500748A (en) 1985-03-15 1986-10-01 Philips Nv COLLIMATOR CHANGE SYSTEM.
JPS61225798A (en) 1985-03-29 1986-10-07 三菱電機株式会社 Plasma generator
US4705955A (en) * 1985-04-02 1987-11-10 Curt Mileikowsky Radiation therapy for cancer patients
US4633125A (en) 1985-05-09 1986-12-30 Board Of Trustees Operating Michigan State University Vented 360 degree rotatable vessel for containing liquids
US4628523A (en) 1985-05-13 1986-12-09 B.V. Optische Industrie De Oude Delft Direction control for radiographic therapy apparatus
JPS62150804A (en) 1985-12-25 1987-07-04 Sumitomo Electric Ind Ltd Charged particle deflector for synchrotron orbit radiation system
JPS62186500A (en) 1986-02-12 1987-08-14 三菱電機株式会社 Charged beam device
US4783634A (en) 1986-02-27 1988-11-08 Mitsubishi Denki Kabushiki Kaisha Superconducting synchrotron orbital radiation apparatus
JPS62150804U (en) 1986-03-14 1987-09-24
US4739173A (en) 1986-04-11 1988-04-19 Board Of Trustees Operating Michigan State University Collimator apparatus and method
JPS62186500U (en) 1986-05-20 1987-11-27
US4763483A (en) 1986-07-17 1988-08-16 Helix Technology Corporation Cryopump and method of starting the cryopump
US4736106A (en) 1986-10-08 1988-04-05 Michigan State University Method and apparatus for uniform charged particle irradiation of a surface
JP2670670B2 (en) 1986-12-12 1997-10-29 日鉱金属 株式会社 High strength and high conductivity copper alloy
DE3644536C1 (en) 1986-12-24 1987-11-19 Basf Lacke & Farben Device for a water-based paint application with high-speed rotary atomizers via direct charging or contact charging
GB8701363D0 (en) 1987-01-22 1987-02-25 Oxford Instr Ltd Magnetic field generating assembly
JP2543869B2 (en) 1987-02-12 1996-10-16 株式会社東芝 Superconducting rotor
JPS63218200A (en) 1987-03-05 1988-09-12 Furukawa Electric Co Ltd:The Superconductive sor generation device
JPS63226899A (en) 1987-03-16 1988-09-21 Ishikawajima Harima Heavy Ind Co Ltd Superconductive wigller
JPH0517318Y2 (en) 1987-03-24 1993-05-10
US4767930A (en) 1987-03-31 1988-08-30 Siemens Medical Laboratories, Inc. Method and apparatus for enlarging a charged particle beam
JPH0546928Y2 (en) 1987-04-01 1993-12-09
JPS6435838A (en) 1987-07-31 1989-02-06 Jeol Ltd Charged particle beam device
JPS6489621A (en) 1987-09-30 1989-04-04 Nec Corp Frequency synthesizer
US4796432A (en) 1987-10-09 1989-01-10 Unisys Corporation Long hold time cryogens dewar
GB8725459D0 (en) 1987-10-30 1987-12-02 Nat Research Dev Corpn Generating particle beams
US4945478A (en) 1987-11-06 1990-07-31 Center For Innovative Technology Noninvasive medical imaging system and method for the identification and 3-D display of atherosclerosis and the like
US4803433A (en) 1987-12-21 1989-02-07 Montefiore Hospital Association Of Western Pennsylvania, Inc. Method and apparatus for shimming tubular supermagnets
US4870287A (en) 1988-03-03 1989-09-26 Loma Linda University Medical Center Multi-station proton beam therapy system
US4845371A (en) 1988-03-29 1989-07-04 Siemens Medical Laboratories, Inc. Apparatus for generating and transporting a charged particle beam
JP2645314B2 (en) 1988-04-28 1997-08-25 清水建設株式会社 Magnetic shield
US5006759A (en) 1988-05-09 1991-04-09 Siemens Medical Laboratories, Inc. Two piece apparatus for accelerating and transporting a charged particle beam
JPH079839B2 (en) 1988-05-30 1995-02-01 株式会社島津製作所 High frequency multipole accelerator
JPH078300B2 (en) 1988-06-21 1995-02-01 三菱電機株式会社 Charged particle beam irradiation device
US4880985A (en) 1988-10-05 1989-11-14 Douglas Jones Detached collimator apparatus for radiation therapy
US5046078A (en) 1989-08-31 1991-09-03 Siemens Medical Laboratories, Inc. Apparatus and method for inhibiting the generation of excessive radiation
US5010562A (en) 1989-08-31 1991-04-23 Siemens Medical Laboratories, Inc. Apparatus and method for inhibiting the generation of excessive radiation
US5072123A (en) 1990-05-03 1991-12-10 Varian Associates, Inc. Method of measuring total ionization current in a segmented ionization chamber
JP2593576B2 (en) 1990-07-31 1997-03-26 株式会社東芝 Radiation positioning device
JPH0494198A (en) 1990-08-09 1992-03-26 Nippon Steel Corp Electro-magnetic shield material
JP2896217B2 (en) 1990-09-21 1999-05-31 キヤノン株式会社 Recording device
JP3215409B2 (en) 1990-09-19 2001-10-09 セイコーインスツルメンツ株式会社 Light valve device
US5097132A (en) * 1990-11-21 1992-03-17 Picker International, Inc. Nuclear medicine camera system with improved gantry and patient table
JP2786330B2 (en) 1990-11-30 1998-08-13 株式会社日立製作所 Superconducting magnet coil and curable resin composition used for the magnet coil
JPH087998Y2 (en) 1990-12-28 1996-03-06 株式会社小松製作所 Breakthrough shock absorber for press machine
DE4101094C1 (en) 1991-01-16 1992-05-27 Kernforschungszentrum Karlsruhe Gmbh, 7500 Karlsruhe, De Superconducting micro-undulator for particle accelerator synchrotron source - has superconductor which produces strong magnetic field along track and allows intensity and wavelength of radiation to be varied by conrolling current
IT1244689B (en) 1991-01-25 1994-08-08 Getters Spa DEVICE TO ELIMINATE HYDROGEN FROM A VACUUM CHAMBER, AT CRYOGENIC TEMPERATURES, ESPECIALLY IN HIGH ENERGY PARTICLE ACCELERATORS
JPH04258781A (en) 1991-02-14 1992-09-14 Toshiba Corp Scintillation camera
JPH04273409A (en) 1991-02-28 1992-09-29 Hitachi Ltd Superconducting magnet device; particle accelerator using said superconducting magnet device
EP0508151B1 (en) 1991-03-13 1998-08-12 Fujitsu Limited Charged particle beam exposure system and charged particle beam exposure method
JP2556057Y2 (en) 1991-05-11 1997-12-03 ケージーパック株式会社 Temporary denture storage bag
JPH04337300A (en) 1991-05-15 1992-11-25 Res Dev Corp Of Japan Superconducting deflection magnet
JP2540900Y2 (en) 1991-05-16 1997-07-09 株式会社シマノ Spinning reel stopper device
US5148032A (en) 1991-06-28 1992-09-15 Siemens Medical Laboratories, Inc. Radiation emitting device with moveable aperture plate
WO1993002537A1 (en) 1991-07-16 1993-02-04 Sergei Nikolaevich Lapitsky Superconducting electromagnet for charged-particle accelerator
US5166531A (en) 1991-08-05 1992-11-24 Varian Associates, Inc. Leaf-end configuration for multileaf collimator
JP3125805B2 (en) 1991-10-16 2001-01-22 株式会社日立製作所 Circular accelerator
JPH0636893Y2 (en) 1991-11-16 1994-09-28 三友工業株式会社 Continuous thermoforming equipment
US5374913A (en) 1991-12-13 1994-12-20 Houston Advanced Research Center Twin-bore flux pipe dipole magnet
NL9200286A (en) 1992-02-17 1993-09-16 Sven Ploem IMPACT-FREE OPERATING SYSTEM FOR A MULTI-AXLE DRIVER MANIPULATOR.
US5260581A (en) 1992-03-04 1993-11-09 Loma Linda University Medical Center Method of treatment room selection verification in a radiation beam therapy system
JPH05341352A (en) 1992-06-08 1993-12-24 Minolta Camera Co Ltd Camera and cap for bayonet mount of interchangeable lens
JPH0636893A (en) 1992-06-11 1994-02-10 Ishikawajima Harima Heavy Ind Co Ltd Particle accelerator
JP2824363B2 (en) 1992-07-15 1998-11-11 三菱電機株式会社 Beam supply device
JP3121157B2 (en) 1992-12-15 2000-12-25 株式会社日立メディコ Microtron electron accelerator
US5394130A (en) 1993-01-07 1995-02-28 General Electric Company Persistent superconducting switch for conduction-cooled superconducting magnet
JPH06233831A (en) 1993-02-10 1994-08-23 Hitachi Medical Corp Stereotaxic radiotherapeutic device
US5464411A (en) 1993-11-02 1995-11-07 Loma Linda University Medical Center Vacuum-assisted fixation apparatus
US5549616A (en) 1993-11-02 1996-08-27 Loma Linda University Medical Center Vacuum-assisted stereotactic fixation system with patient-activated switch
US5463291A (en) 1993-12-23 1995-10-31 Carroll; Lewis Cyclotron and associated magnet coil and coil fabricating process
JPH07191199A (en) 1993-12-27 1995-07-28 Fujitsu Ltd Method and system for exposure with charged particle beam
US5410286A (en) 1994-02-25 1995-04-25 General Electric Company Quench-protected, refrigerated superconducting magnet
JP3307059B2 (en) 1994-03-17 2002-07-24 株式会社日立製作所 Accelerator, medical device and emission method
JPH07260939A (en) 1994-03-17 1995-10-13 Hitachi Medical Corp Collimator replacement carriage for scintillation camera
JPH07263196A (en) 1994-03-18 1995-10-13 Toshiba Corp High frequency acceleration cavity
JP3079346B2 (en) * 1994-03-18 2000-08-21 住友重機械工業株式会社 3D particle beam irradiation equipment
DE4411171A1 (en) * 1994-03-30 1995-10-05 Siemens Ag Compact charged-particle accelerator for tumour therapy
US5485730A (en) 1994-08-10 1996-01-23 General Electric Company Remote cooling system for a superconducting magnet
EP0840538A3 (en) 1994-08-19 1999-06-16 Nycomed Amersham plc Target for use in the production of heavy isotopes
IT1281184B1 (en) * 1994-09-19 1998-02-17 Giorgio Trozzi Amministratore EQUIPMENT FOR INTRAOPERATIVE RADIOTHERAPY BY MEANS OF LINEAR ACCELERATORS THAT CAN BE USED DIRECTLY IN THE OPERATING ROOM
EP0709618B1 (en) 1994-10-27 2002-10-09 General Electric Company Ceramic superconducting lead
US5633747A (en) 1994-12-21 1997-05-27 Tencor Instruments Variable spot-size scanning apparatus
JP3629054B2 (en) 1994-12-22 2005-03-16 北海製罐株式会社 Surface correction coating method for welded can side seam
US5585642A (en) 1995-02-15 1996-12-17 Loma Linda University Medical Center Beamline control and security system for a radiation treatment facility
US5510357A (en) 1995-02-28 1996-04-23 Eli Lilly And Company Benzothiophene compounds as anti-estrogenic agents
JP3023533B2 (en) 1995-03-23 2000-03-21 住友重機械工業株式会社 cyclotron
JP3118608B2 (en) 1995-04-18 2000-12-18 ロマ リンダ ユニヴァーシティ メディカル センター System for multi-particle therapy
US5668371A (en) 1995-06-06 1997-09-16 Wisconsin Alumni Research Foundation Method and apparatus for proton therapy
BE1009669A3 (en) 1995-10-06 1997-06-03 Ion Beam Applic Sa Method of extraction out of a charged particle isochronous cyclotron and device applying this method.
JPH09162585A (en) 1995-12-05 1997-06-20 Kanazawa Kogyo Univ Magnetic shielding room and its assembling method
JP3472657B2 (en) * 1996-01-18 2003-12-02 三菱電機株式会社 Particle beam irradiation equipment
JP3121265B2 (en) 1996-05-07 2000-12-25 株式会社日立製作所 Radiation shield
US5811944A (en) 1996-06-25 1998-09-22 The United States Of America As Represented By The Department Of Energy Enhanced dielectric-wall linear accelerator
US5821705A (en) 1996-06-25 1998-10-13 The United States Of America As Represented By The United States Department Of Energy 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
EP1378266A1 (en) 1996-08-30 2004-01-07 Hitachi, Ltd. Charged particle beam apparatus
JPH1071213A (en) 1996-08-30 1998-03-17 Hitachi Ltd Proton ray treatment system
US5851182A (en) 1996-09-11 1998-12-22 Sahadevan; Velayudhan 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
US5727554A (en) 1996-09-19 1998-03-17 University Of Pittsburgh Of The Commonwealth System Of Higher Education Apparatus responsive to movement of a patient during treatment/diagnosis
US6111749A (en) 1996-09-25 2000-08-29 International Business Machines Corporation Flexible cold plate having a one-piece coolant conduit and method employing same
US5672878A (en) 1996-10-24 1997-09-30 Siemens Medical Systems Inc. Ionization chamber having off-passageway measuring electrodes
US5920601A (en) 1996-10-25 1999-07-06 Lockheed Martin Idaho Technologies Company System and method for delivery of neutron beams for medical therapy
US5825845A (en) 1996-10-28 1998-10-20 Loma Linda University Medical Center Proton beam digital imaging system
US5784431A (en) 1996-10-29 1998-07-21 University Of Pittsburgh Of The Commonwealth System Of Higher Education Apparatus for matching X-ray images with reference images
JP3841898B2 (en) 1996-11-21 2006-11-08 三菱電機株式会社 Deep dose measurement system
JP3784419B2 (en) 1996-11-26 2006-06-14 三菱電機株式会社 Method for forming an energy distribution
JP3246364B2 (en) 1996-12-03 2002-01-15 株式会社日立製作所 Synchrotron accelerator and medical device using the same
US5998889A (en) 1996-12-10 1999-12-07 Nikon Corporation Electro-magnetic motor cooling system
EP0864337A3 (en) 1997-03-15 1999-03-10 Shenzhen OUR International Technology & Science Co., Ltd. Three-dimensional irradiation technique with charged particles of Bragg peak properties and its device
JPH10300899A (en) * 1997-04-22 1998-11-13 Mitsubishi Electric Corp Radiation therapeutic device
US5841237A (en) 1997-07-14 1998-11-24 Lockheed Martin Energy Research Corporation Production of large resonant plasma volumes in microwave electron cyclotron resonance ion sources
BE1012534A3 (en) 1997-08-04 2000-12-05 Sumitomo Heavy Industries Bed system for radiation therapy.
US5846043A (en) 1997-08-05 1998-12-08 Spath; John J. Cart and caddie system for storing and delivering water bottles
US5931638A (en) 1997-08-07 1999-08-03 United Technologies Corporation Turbomachinery airfoil with optimized heat transfer
JP3532739B2 (en) 1997-08-07 2004-05-31 住友重機械工業株式会社 Radiation field forming member fixing device
US5963615A (en) 1997-08-08 1999-10-05 Siemens Medical Systems, Inc. Rotational flatness improvement
JP3519248B2 (en) 1997-08-08 2004-04-12 住友重機械工業株式会社 Rotation irradiation room for radiation therapy
JP3203211B2 (en) 1997-08-11 2001-08-27 住友重機械工業株式会社 Water phantom type dose distribution measuring device and radiotherapy device
JPH11102800A (en) 1997-09-29 1999-04-13 Toshiba Corp Superconducting high-frequency accelerating cavity and particle accelerator
EP0943148A1 (en) 1997-10-06 1999-09-22 Koninklijke Philips Electronics N.V. X-ray examination apparatus including adjustable x-ray filter and collimator
JP3577201B2 (en) 1997-10-20 2004-10-13 三菱電機株式会社 Charged particle beam irradiation device, charged particle beam rotation irradiation device, and charged particle beam irradiation method
JPH11142600A (en) 1997-11-12 1999-05-28 Mitsubishi Electric Corp Charged particle beam irradiation device and irradiation method
JP3528583B2 (en) 1997-12-25 2004-05-17 三菱電機株式会社 Charged particle beam irradiation device and magnetic field generator
JP2002500190A (en) * 1998-01-08 2002-01-08 ザ リージェンツ オブ ザ ユニバーシティ オブ カリフォルニア Kinesin motor modulators derived from marine sponges
US6118848A (en) 1998-01-14 2000-09-12 Reiffel; Leonard System to stabilize an irradiated internal target
AUPP156698A0 (en) 1998-01-30 1998-02-19 Pacific Solar Pty Limited New method for hydrogen passivation
JPH11243295A (en) 1998-02-26 1999-09-07 Shimizu Corp Magnetic shield method and structure
JPH11253563A (en) 1998-03-10 1999-09-21 Hitachi Ltd Method and device for charged particle beam radiation
JP3053389B1 (en) 1998-12-03 2000-06-19 三菱電機株式会社 Moving object tracking irradiation device
JPH11288809A (en) 1998-03-31 1999-10-19 Toshiba Corp Superconducting magnet
GB2361523B (en) 1998-03-31 2002-05-01 Toshiba Kk Superconducting magnet apparatus
JPH11329945A (en) 1998-05-08 1999-11-30 Nikon Corp Method and system for charged beam transfer
CA2241116C (en) 1998-06-19 2009-08-25 Liyan Zhang Radiation (e.g. x-ray pulse) generator mechanisms
US6376943B1 (en) 1998-08-26 2002-04-23 American Superconductor Corporation Superconductor rotor cooling system
JP2000070389A (en) 1998-08-27 2000-03-07 Mitsubishi Electric Corp Exposure value computing device, exposure value computing, and recording medium
EP1115997A2 (en) 1998-09-14 2001-07-18 Massachusetts Institute Of Technology Superconducting apparatuses and cooling methods
SE513192C2 (en) 1998-09-29 2000-07-24 Gems Pet Systems Ab Procedures and systems for HF control
US6369585B2 (en) 1998-10-02 2002-04-09 Siemens Medical Solutions Usa, Inc. System and method for tuning a resonant structure
US6621889B1 (en) 1998-10-23 2003-09-16 Varian Medical Systems, Inc. Method and system for predictive physiological gating of radiation therapy
US6279579B1 (en) 1998-10-23 2001-08-28 Varian Medical Systems, Inc. Method and system for positioning patients for medical treatment procedures
US6241671B1 (en) 1998-11-03 2001-06-05 Stereotaxis, Inc. Open field system for magnetic surgery
US6441569B1 (en) 1998-12-09 2002-08-27 Edward F. Janzow Particle accelerator for inducing contained particle collisions
BE1012358A5 (en) 1998-12-21 2000-10-03 Ion Beam Applic Sa Process of changes of energy of particle beam extracted of an accelerator and device for this purpose.
BE1012371A5 (en) 1998-12-24 2000-10-03 Ion Beam Applic Sa Treatment method for proton beam and device applying the method.
JP2000237335A (en) 1999-02-17 2000-09-05 Mitsubishi Electric Corp Radiotherapy method and system
DE19907774A1 (en) 1999-02-19 2000-08-31 Schwerionenforsch Gmbh Method for verifying the calculated radiation dose of an ion beam therapy system
DE19907065A1 (en) 1999-02-19 2000-08-31 Schwerionenforsch Gmbh Method for checking an isocenter and a patient positioning device of an ion beam therapy system
DE19907121A1 (en) 1999-02-19 2000-08-31 Schwerionenforsch Gmbh Procedure for checking the beam guidance of an ion beam therapy system
DE19907098A1 (en) 1999-02-19 2000-08-24 Schwerionenforsch Gmbh Ion beam scanning system for radiation therapy e.g. for tumor treatment, uses energy absorption device displaced transverse to ion beam path via linear motor for altering penetration depth
US6144875A (en) 1999-03-16 2000-11-07 Accuray Incorporated Apparatus and method for compensating for respiratory and patient motion during treatment
EP1041579A1 (en) 1999-04-01 2000-10-04 GSI Gesellschaft für Schwerionenforschung mbH Gantry with an ion-optical system
EP1175244B1 (en) 1999-04-07 2009-06-03 Loma Linda University Medical Center Patient motion monitoring system for proton therapy
JP2000294399A (en) 1999-04-12 2000-10-20 Toshiba Corp Superconducting high-frequency acceleration cavity and particle accelerator
JP3530072B2 (en) 1999-05-13 2004-05-24 三菱電機株式会社 Control device for radiation irradiation apparatus for radiation therapy
SE9902163D0 (en) 1999-06-09 1999-06-09 Scanditronix Medical Ab Stable rotable radiation gantry
JP2001006900A (en) 1999-06-18 2001-01-12 Toshiba Corp Radiant light generation device
EP1189661B1 (en) * 1999-06-25 2012-11-28 Paul Scherrer Institut Device for carrying out proton therapy
JP2001009050A (en) 1999-06-29 2001-01-16 Hitachi Medical Corp Radiotherapy device
EP1069809A1 (en) 1999-07-13 2001-01-17 Ion Beam Applications S.A. Isochronous cyclotron and method of extraction of charged particles from such cyclotron
WO2001006524A2 (en) 1999-07-14 2001-01-25 E.I. Du Pont De Nemours And Company Superconducting coil assembly
JP2001029490A (en) 1999-07-19 2001-02-06 Hitachi Ltd Combined irradiation evaluation support system
NL1012677C2 (en) 1999-07-22 2001-01-23 William Van Der Burg Device and method for placing an information carrier.
US6380545B1 (en) 1999-08-30 2002-04-30 Southeastern Universities Research Association, Inc. Uniform raster pattern generating system
US6420917B1 (en) 1999-10-01 2002-07-16 Ericsson Inc. PLL loop filter with switched-capacitor resistor
US6713773B1 (en) 1999-10-07 2004-03-30 Mitec, Inc. Irradiation system and method
WO2001026569A1 (en) 1999-10-08 2001-04-19 Advanced Research & Technology Institute Apparatus and method for non-invasive myocardial revascularization
JP4185637B2 (en) 1999-11-01 2008-11-26 株式会社神鋼エンジニアリング&メンテナンス Rotating irradiation chamber for particle beam therapy
JP2001137372A (en) * 1999-11-10 2001-05-22 Mitsubishi Electric Corp Method for installation of radiation device, in radiation room and irradiation chamber
US6803585B2 (en) 2000-01-03 2004-10-12 Yuri Glukhoy Electron-cyclotron resonance type ion beam source for ion implanter
US6366021B1 (en) 2000-01-06 2002-04-02 Varian Medical Systems, Inc. Standing wave particle beam accelerator with switchable beam energy
JP4128717B2 (en) 2000-01-26 2008-07-30 古河電気工業株式会社 Floor heating panel
JP3927348B2 (en) * 2000-03-15 2007-06-06 三菱電機株式会社 Rotating irradiation device
US6498444B1 (en) 2000-04-10 2002-12-24 Siemens Medical Solutions Usa, Inc. Computer-aided tuning of charged particle accelerators
AU2001274814B2 (en) 2000-04-27 2004-04-01 Loma Linda University Nanodosimeter based on single ion detection
JP2001346893A (en) 2000-06-06 2001-12-18 Ishikawajima Harima Heavy Ind Co Ltd Radiotherapeutic apparatus
JP3705091B2 (en) 2000-07-27 2005-10-12 株式会社日立製作所 Medical accelerator system and operating method thereof
US6914396B1 (en) 2000-07-31 2005-07-05 Yale University Multi-stage cavity cyclotron resonance accelerator
US7041479B2 (en) 2000-09-06 2006-05-09 The Board Of Trustess Of The Leland Stanford Junior University Enhanced in vitro synthesis of active proteins containing disulfide bonds
JP2002102198A (en) 2000-09-22 2002-04-09 Ge Medical Systems Global Technology Co Llc Mr apparatus
CA2325362A1 (en) 2000-11-08 2002-05-08 Kirk Flippo Method and apparatus for high-energy generation and for inducing nuclear reactions
DE10057664A1 (en) 2000-11-21 2002-05-29 Siemens Ag Superconducting device with a cold head of a refrigeration unit thermally coupled to a rotating, superconducting winding
US6714694B1 (en) * 2000-11-27 2004-03-30 Xerox Corporation Method for sliding window image processing of associative operators
JP3633475B2 (en) 2000-11-27 2005-03-30 鹿島建設株式会社 Interdigital transducer method and panel, and magnetic darkroom
AU3071802A (en) 2000-12-08 2002-06-18 Univ Loma Linda Med Proton beam therapy control system
US6492922B1 (en) 2000-12-14 2002-12-10 Xilinx Inc. Anti-aliasing filter with automatic cutoff frequency adaptation
JP2002210028A (en) 2001-01-23 2002-07-30 Mitsubishi Electric Corp Radiation irradiating system and radiation irradiating method
JP3995089B2 (en) 2001-02-05 2007-10-24 ジー エス アイ ゲゼルシャフト フュア シュベールイオーネンフォルシュンク エム ベー ハー Device for pre-acceleration of ion beam used in heavy ion beam application system
ATE485591T1 (en) 2001-02-06 2010-11-15 Gsi Helmholtzzentrum Schwerionenforschung Gmbh BEAM SCANNING SYSTEM FOR HEAVY ION GANTRY
US6493424B2 (en) 2001-03-05 2002-12-10 Siemens Medical Solutions Usa, Inc. Multi-mode operation of a standing wave linear accelerator
JP2002263090A (en) 2001-03-07 2002-09-17 Mitsubishi Heavy Ind Ltd Examination treatment apparatus
JP4115675B2 (en) 2001-03-14 2008-07-09 三菱電機株式会社 Absorption dosimetry device for intensity modulation therapy
US6646383B2 (en) 2001-03-15 2003-11-11 Siemens Medical Solutions Usa, Inc. Monolithic structure with asymmetric coupling
US6708054B2 (en) * 2001-04-12 2004-03-16 Koninklijke Philips Electronics, N.V. MR-based real-time radiation therapy oncology simulator
US6465957B1 (en) 2001-05-25 2002-10-15 Siemens Medical Solutions Usa, Inc. Standing wave linear accelerator with integral prebunching section
EP1265462A1 (en) 2001-06-08 2002-12-11 Ion Beam Applications S.A. Device and method for the intensity control of a beam extracted from a particle accelerator
WO2003017745A2 (en) 2001-08-23 2003-03-06 Sciperio, Inc. Architecture tool and methods of use
CA2456106C (en) 2001-08-24 2012-06-12 Mitsubishi Heavy Industries, Ltd. Radiation treatment apparatus
JP2003086400A (en) 2001-09-11 2003-03-20 Hitachi Ltd Accelerator system and medical accelerator facility
JP3948511B2 (en) * 2001-10-26 2007-07-25 独立行政法人科学技術振興機構 Magnetic field generator that combines electromagnet and permanent magnet in the vertical direction
WO2003039212A1 (en) 2001-10-30 2003-05-08 Loma Linda University Medical Center Method and device for delivering radiotherapy
US7221733B1 (en) 2002-01-02 2007-05-22 Varian Medical Systems Technologies, Inc. Method and apparatus for irradiating a target
US6593696B2 (en) 2002-01-04 2003-07-15 Siemens Medical Solutions Usa, Inc. Low dark current linear accelerator
JP3750930B2 (en) 2002-01-17 2006-03-01 三菱電機株式会社 Charged particle irradiation equipment
DE10205949B4 (en) 2002-02-12 2013-04-25 Gsi Helmholtzzentrum Für Schwerionenforschung Gmbh A method and apparatus for controlling a raster scan irradiation apparatus for heavy ions or protons with beam extraction
JP3691020B2 (en) 2002-02-28 2005-08-31 株式会社日立製作所 Medical charged particle irradiation equipment
JP4337300B2 (en) 2002-02-28 2009-09-30 日立金属株式会社 Rare earth permanent magnet manufacturing method
JP4072359B2 (en) 2002-02-28 2008-04-09 株式会社日立製作所 Charged particle beam irradiation equipment
JP3801938B2 (en) 2002-03-26 2006-07-26 株式会社日立製作所 Particle beam therapy system and method for adjusting charged particle beam trajectory
EP1358908A1 (en) 2002-05-03 2003-11-05 Ion Beam Applications S.A. Device for irradiation therapy with charged particles
US6735277B2 (en) 2002-05-23 2004-05-11 Koninklijke Philips Electronics N.V. Inverse planning for intensity-modulated radiotherapy
EP1531902A1 (en) 2002-05-31 2005-05-25 Ion Beam Applications S.A. Apparatus for irradiating a target volume
US6777700B2 (en) 2002-06-12 2004-08-17 Hitachi, Ltd. Particle beam irradiation system and method of adjusting irradiation apparatus
US7162005B2 (en) 2002-07-19 2007-01-09 Varian Medical Systems Technologies, Inc. Radiation sources and compact radiation scanning systems
JP3748426B2 (en) 2002-09-30 2006-02-22 株式会社日立製作所 Medical particle beam irradiation equipment
JP3961925B2 (en) 2002-10-17 2007-08-22 三菱電機株式会社 Beam accelerator
US6853142B2 (en) 2002-11-04 2005-02-08 Zond, Inc. Methods and apparatus for generating high-density plasma
JP4653489B2 (en) 2002-11-25 2011-03-16 イヨン ベアム アプリカスィヨン エッス.アー. Cyclotron and how to use it
EP1429345A1 (en) 2002-12-10 2004-06-16 Ion Beam Applications S.A. Device and method of radioisotope production
DE10261099B4 (en) * 2002-12-20 2005-12-08 Siemens Ag Ion beam system
US6822244B2 (en) 2003-01-02 2004-11-23 Loma Linda University Medical Center Configuration management and retrieval system for proton beam therapy system
US20060104858A1 (en) * 2003-01-06 2006-05-18 Potember Richard S Hydroxyl free radical-induced decontamination of airborne spores, viruses and bacteria in a dynamic system
EP1439566B1 (en) 2003-01-17 2019-08-28 ICT, Integrated Circuit Testing Gesellschaft für Halbleiterprüftechnik mbH Charged particle beam apparatus and method for operating the same
US7814937B2 (en) * 2005-10-26 2010-10-19 University Of Southern California Deployable contour crafting
JP4186636B2 (en) 2003-01-30 2008-11-26 株式会社日立製作所 Superconducting magnet
CN100359993C (en) 2003-02-17 2008-01-02 三菱电机株式会社 Charged particle accelerator
US6812462B1 (en) 2003-02-21 2004-11-02 Kla-Tencor Technologies Corporation Dual electron beam instrument for multi-perspective
JP3748433B2 (en) 2003-03-05 2006-02-22 株式会社日立製作所 Bed positioning device and positioning method thereof
JP3859605B2 (en) 2003-03-07 2006-12-20 株式会社日立製作所 Particle beam therapy system and particle beam extraction method
WO2004084603A1 (en) 2003-03-17 2004-09-30 Kajima Corporation Open magnetic shield structure and its magnetic frame
JP3655292B2 (en) 2003-04-14 2005-06-02 株式会社日立製作所 Particle beam irradiation apparatus and method for adjusting charged particle beam irradiation apparatus
EP1477206B2 (en) 2003-05-13 2011-02-23 Hitachi, Ltd. Particle beam irradiation apparatus and treatment planning unit
ATE367187T1 (en) 2003-05-13 2007-08-15 Ion Beam Applic Sa METHOD AND SYSTEM FOR AUTOMATIC BEAM ALLOCATION IN A PARTICLE BEAM THERAPY FACILITY WITH MULTIPLE ROOMS
JP2005027681A (en) 2003-07-07 2005-02-03 Hitachi Ltd Treatment device using charged particle and treatment system using charged particle
US7199382B2 (en) 2003-08-12 2007-04-03 Loma Linda University Medical Center Patient alignment system with external measurement and object coordination for radiation therapy system
WO2005018735A2 (en) 2003-08-12 2005-03-03 Loma Linda University Medical Center Modular patient support system
KR20050021733A (en) 2003-08-25 2005-03-07 삼성전자주식회사 Storage medium for storing copy protection data, modulation method, storage apparatus and reproducing apparatus
JP4323267B2 (en) 2003-09-09 2009-09-02 株式会社ミツトヨ Shape measuring device, shape measuring method, shape analyzing device, shape analyzing program, and recording medium
JP3685194B2 (en) 2003-09-10 2005-08-17 株式会社日立製作所 Particle beam therapy device, range modulation rotation device, and method of attaching range modulation rotation device
JP4129768B2 (en) 2003-10-02 2008-08-06 株式会社山武 Detection device
JP4177740B2 (en) 2003-10-10 2008-11-05 株式会社日立製作所 Superconducting magnet for MRI
US7557361B2 (en) 2003-10-16 2009-07-07 Alis Corporation Ion sources, systems and methods
US7557359B2 (en) 2003-10-16 2009-07-07 Alis Corporation Ion sources, systems and methods
US7557358B2 (en) 2003-10-16 2009-07-07 Alis Corporation Ion sources, systems and methods
US7786451B2 (en) 2003-10-16 2010-08-31 Alis Corporation Ion sources, systems and methods
US7554096B2 (en) 2003-10-16 2009-06-30 Alis Corporation Ion sources, systems and methods
US7554097B2 (en) 2003-10-16 2009-06-30 Alis Corporation Ion sources, systems and methods
US7786452B2 (en) 2003-10-16 2010-08-31 Alis Corporation Ion sources, systems and methods
US7557360B2 (en) 2003-10-16 2009-07-07 Alis Corporation Ion sources, systems and methods
US7154991B2 (en) 2003-10-17 2006-12-26 Accuray, Inc. Patient positioning assembly for therapeutic radiation system
CN1537657A (en) * 2003-10-22 2004-10-20 高春平 Radiotherapeutic apparatus in operation
US7295648B2 (en) 2003-10-23 2007-11-13 Elektra Ab (Publ) Method and apparatus for treatment by ionizing radiation
JP4114590B2 (en) 2003-10-24 2008-07-09 株式会社日立製作所 Particle beam therapy system
JP3912364B2 (en) 2003-11-07 2007-05-09 株式会社日立製作所 Particle beam therapy system
WO2005054899A1 (en) 2003-12-04 2005-06-16 Paul Scherrer Institut An inorganic scintillating mixture and a sensor assembly for charged particle dosimetry
JP3643371B1 (en) 2003-12-10 2005-04-27 株式会社日立製作所 Method of adjusting particle beam irradiation apparatus and irradiation field forming apparatus
JP4443917B2 (en) 2003-12-26 2010-03-31 株式会社日立製作所 Particle beam therapy system
US7173385B2 (en) 2004-01-15 2007-02-06 The Regents Of The University Of California Compact accelerator
US7710051B2 (en) 2004-01-15 2010-05-04 Lawrence Livermore National Security, Llc Compact accelerator for medical therapy
JP4273409B2 (en) 2004-01-29 2009-06-03 日本ビクター株式会社 Worm gear device and electronic device including the worm gear device
DE602005002379T2 (en) 2004-02-23 2008-06-12 Zyvex Instruments, LLC, Richardson Use of a probe in a particle beam device
DE102004012452A1 (en) 2004-03-13 2005-10-06 Bruker Biospin Gmbh Superconducting magnet system with pulse tube cooler
EP1584353A1 (en) 2004-04-05 2005-10-12 Paul Scherrer Institut A system for delivery of proton therapy
US7860550B2 (en) 2004-04-06 2010-12-28 Accuray, Inc. Patient positioning assembly
US8160205B2 (en) 2004-04-06 2012-04-17 Accuray Incorporated Robotic arm for patient positioning assembly
JP4257741B2 (en) 2004-04-19 2009-04-22 三菱電機株式会社 Charged particle beam accelerator, particle beam irradiation medical system using charged particle beam accelerator, and method of operating particle beam irradiation medical system
DE102004027071A1 (en) 2004-05-19 2006-01-05 Gesellschaft für Schwerionenforschung mbH Beam feeder for medical particle accelerator has arbitration unit with switching logic, monitoring unit and sequential control and provides direct access of control room of irradiation-active surgery room for particle beam interruption
DE102004028035A1 (en) 2004-06-09 2005-12-29 Gesellschaft für Schwerionenforschung mbH Apparatus and method for compensating for movements of a target volume during ion beam irradiation
DE202004009421U1 (en) 2004-06-16 2005-11-03 Gesellschaft für Schwerionenforschung mbH Particle accelerator for ion beam radiation therapy
US7073508B2 (en) 2004-06-25 2006-07-11 Loma Linda University Medical Center Method and device for registration and immobilization
US7135678B2 (en) 2004-07-09 2006-11-14 Credence Systems Corporation Charged particle guide
ES2558978T3 (en) 2004-07-21 2016-02-09 Mevion Medical Systems, Inc. Programmable radiofrequency waveform generator for a synchro-cyclotron
US6965116B1 (en) 2004-07-23 2005-11-15 Applied Materials, Inc. Method of determining dose uniformity of a scanning ion implanter
JP4489529B2 (en) 2004-07-28 2010-06-23 株式会社日立製作所 Particle beam therapy system and control system for particle beam therapy system
GB2418061B (en) 2004-09-03 2006-10-18 Zeiss Carl Smt Ltd Scanning particle beam instrument
JP2006128087A (en) 2004-09-30 2006-05-18 Hitachi Ltd Charged particle beam emitting device and charged particle beam emitting method
JP3806723B2 (en) 2004-11-16 2006-08-09 株式会社日立製作所 Particle beam irradiation system
US7265356B2 (en) * 2004-11-29 2007-09-04 The University Of Chicago Image-guided medical intervention apparatus and method
DE102004057726B4 (en) 2004-11-30 2010-03-18 Siemens Ag Medical examination and treatment facility
CN100561332C (en) 2004-12-09 2009-11-18 Ge医疗系统环球技术有限公司 X-ray irradiation device and x-ray imaging equipment
US7994664B2 (en) 2004-12-10 2011-08-09 General Electric Company System and method for cooling a superconducting rotary machine
US7122966B2 (en) 2004-12-16 2006-10-17 General Electric Company Ion source apparatus and method
DE102004061869B4 (en) 2004-12-22 2008-06-05 Siemens Ag Device for superconductivity and magnetic resonance device
EP1842079A4 (en) 2004-12-30 2010-07-07 Crystalview Medical Imaging Lt Clutter suppression in ultrasonic imaging systems
US7349730B2 (en) 2005-01-11 2008-03-25 Moshe Ein-Gal Radiation modulator positioner
US7997553B2 (en) 2005-01-14 2011-08-16 Indiana University Research & Technology Corporati Automatic retractable floor system for a rotating gantry
US7193227B2 (en) 2005-01-24 2007-03-20 Hitachi, Ltd. Ion beam therapy system and its couch positioning method
US7468506B2 (en) 2005-01-26 2008-12-23 Applied Materials, Israel, Ltd. Spot grid array scanning system
US7525104B2 (en) 2005-02-04 2009-04-28 Mitsubishi Denki Kabushiki Kaisha Particle beam irradiation method and particle beam irradiation apparatus used for the same
GB2422958B (en) 2005-02-04 2008-07-09 Siemens Magnet Technology Ltd Quench protection circuit for a superconducting magnet
JP4679567B2 (en) 2005-02-04 2011-04-27 三菱電機株式会社 Particle beam irradiation equipment
JP4219905B2 (en) 2005-02-25 2009-02-04 株式会社日立製作所 Rotating gantry for radiation therapy equipment
DE602005027128D1 (en) 2005-03-09 2011-05-05 Scherrer Inst Paul SYSTEM FOR SIMULTANEOUS RECORDING OF FIELD BEV (BEAM-EYE-VIEW) X-RAY IMAGES AND ADMINISTRATION OF PROTON THERAPY
JP4363344B2 (en) 2005-03-15 2009-11-11 三菱電機株式会社 Particle beam accelerator
GB0505903D0 (en) 2005-03-23 2005-04-27 Siemens Magnet Technology Ltd A cryogen tank for cooling equipment
JP4751635B2 (en) 2005-04-13 2011-08-17 株式会社日立ハイテクノロジーズ Magnetic field superposition type electron gun
JP4158931B2 (en) 2005-04-13 2008-10-01 三菱電機株式会社 Particle beam therapy system
US7420182B2 (en) 2005-04-27 2008-09-02 Busek Company Combined radio frequency and hall effect ion source and plasma accelerator system
US7014361B1 (en) 2005-05-11 2006-03-21 Moshe Ein-Gal Adaptive rotator for gantry
US7476867B2 (en) 2005-05-27 2009-01-13 Iba Device and method for quality assurance and online verification of radiation therapy
US7575242B2 (en) 2005-06-16 2009-08-18 Siemens Medical Solutions Usa, Inc. Collimator change cart
GB2427478B (en) 2005-06-22 2008-02-20 Siemens Magnet Technology Ltd Particle radiation therapy equipment and method for simultaneous application of magnetic resonance imaging and particle radiation
US7436932B2 (en) 2005-06-24 2008-10-14 Varian Medical Systems Technologies, Inc. X-ray radiation sources with low neutron emissions for radiation scanning
JP3882843B2 (en) * 2005-06-30 2007-02-21 株式会社日立製作所 Rotating irradiation device
WO2007009084A1 (en) 2005-07-13 2007-01-18 Crown Equipment Corporation Pallet clamping device
WO2007014104A2 (en) 2005-07-22 2007-02-01 Tomotherapy Incorporated System and method of evaluating dose delivered by a radiation therapy system
JP2009507524A (en) 2005-07-22 2009-02-26 トモセラピー・インコーポレーテッド Method of imposing constraints on a deformation map and system for implementing it
CA2616296A1 (en) 2005-07-22 2007-02-01 Tomotherapy Incorporated System and method of generating contour structures using a dose volume histogram
EP1907984A4 (en) 2005-07-22 2009-10-21 Tomotherapy Inc Method and system for processing data relating to a radiation therapy treatment plan
WO2007014105A2 (en) 2005-07-22 2007-02-01 Tomotherapy Incorporated Method and system for adapting a radiation therapy treatment plan based on a biological model
CA2616301A1 (en) 2005-07-22 2007-02-01 Tomotherapy Incorporated Method and system for evaluating delivered dose
EP1907059A4 (en) 2005-07-22 2009-10-21 Tomotherapy Inc Method of and system for predicting dose delivery
WO2007014108A2 (en) 2005-07-22 2007-02-01 Tomotherapy Incorporated Method and system for evaluating quality assurance criteria in delivery of a treament plan
JP5390855B2 (en) * 2005-07-23 2014-01-15 トモセラピー・インコーポレーテッド Imaging and delivery of radiation therapy using coordinated movement of gantry and treatment table
DE102005038242B3 (en) 2005-08-12 2007-04-12 Siemens Ag Device for expanding a particle energy distribution of a particle beam of a particle therapy system, beam monitoring and beam adjustment unit and method
EP1752992A1 (en) 2005-08-12 2007-02-14 Siemens Aktiengesellschaft Apparatus for the adaption of a particle beam parameter of a particle beam in a particle beam accelerator and particle beam accelerator with such an apparatus
US20070061937A1 (en) * 2005-09-06 2007-03-22 Curle Dennis W Method and apparatus for aerodynamic hat brim and hat
JP5245193B2 (en) 2005-09-07 2013-07-24 株式会社日立製作所 Charged particle beam irradiation system and charged particle beam extraction method
DE102005044408B4 (en) 2005-09-16 2008-03-27 Siemens Ag Particle therapy system, method and apparatus for requesting a particle beam
DE102005044409B4 (en) 2005-09-16 2007-11-29 Siemens Ag Particle therapy system and method for forming a beam path for an irradiation process in a particle therapy system
US7465928B2 (en) * 2005-09-29 2008-12-16 Siemens Medical Solutions Usa, Inc. Apparatus and methods for guiding cables around a rotating gantry of a nuclear medicine camera
US7295649B2 (en) 2005-10-13 2007-11-13 Varian Medical Systems Technologies, Inc. Radiation therapy system and method of using the same
US7658901B2 (en) 2005-10-14 2010-02-09 The Trustees Of Princeton University Thermally exfoliated graphite oxide
JP5376951B2 (en) 2005-10-24 2013-12-25 ローレンス リヴァーモア ナショナル セキュリティ,エルエルシー Optically initiated silicon carbide high voltage switch
US8466415B2 (en) 2005-11-07 2013-06-18 Fibics Incorporated Methods for performing circuit edit operations with low landing energy electron beams
DE102005053719B3 (en) 2005-11-10 2007-07-05 Siemens Ag Particle therapy system, treatment plan and irradiation method for such a particle therapy system
GB2432259B (en) 2005-11-14 2008-01-30 Siemens Magnet Technology Ltd A resin-impregnated superconducting magnet coil comprising a cooling layer
AU2006342170A1 (en) 2005-11-14 2007-10-25 Lawrence Livermore National Security, Llc Cast dielectric composite linear accelerator
CN101361156B (en) 2005-11-18 2012-12-12 梅维昂医疗系统股份有限公司 Charged particle radiation therapy
US7459899B2 (en) 2005-11-21 2008-12-02 Thermo Fisher Scientific Inc. Inductively-coupled RF power source
US7298821B2 (en) 2005-12-12 2007-11-20 Moshe Ein-Gal Imaging and treatment system
EP1795229A1 (en) 2005-12-12 2007-06-13 Ion Beam Applications S.A. Device and method for positioning a patient in a radiation therapy apparatus
DE102005063220A1 (en) 2005-12-22 2007-06-28 GSI Gesellschaft für Schwerionenforschung mbH Patient`s tumor tissue radiating device, has module detecting data of radiation characteristics and detection device, and correlation unit setting data of radiation characteristics and detection device in time relation to each other
US7432516B2 (en) 2006-01-24 2008-10-07 Brookhaven Science Associates, Llc Rapid cycling medical synchrotron and beam delivery system
JP4696965B2 (en) 2006-02-24 2011-06-08 株式会社日立製作所 Charged particle beam irradiation system and charged particle beam extraction method
JP4310319B2 (en) 2006-03-10 2009-08-05 三菱重工業株式会社 Radiotherapy apparatus control apparatus and radiation irradiation method
DE102006011828A1 (en) 2006-03-13 2007-09-20 Gesellschaft für Schwerionenforschung mbH Irradiation verification device for radiotherapy plants, exhibits living cell material, which is locally fixed in the three space coordinates x, y and z in a container with an insert on cell carriers of the insert, and cell carrier holders
DE102006012680B3 (en) 2006-03-20 2007-08-02 Siemens Ag Particle therapy system has rotary gantry that can be moved so as to correct deviation in axial direction of position of particle beam from its desired axial position
JP4644617B2 (en) 2006-03-23 2011-03-02 株式会社日立ハイテクノロジーズ Charged particle beam equipment
JP4762020B2 (en) 2006-03-27 2011-08-31 株式会社小松製作所 Molding method and molded product
JP4730167B2 (en) 2006-03-29 2011-07-20 株式会社日立製作所 Particle beam irradiation system
US7507975B2 (en) 2006-04-21 2009-03-24 Varian Medical Systems, Inc. System and method for high resolution radiation field shaping
US7582886B2 (en) 2006-05-12 2009-09-01 Brookhaven Science Associates, Llc Gantry for medical particle therapy facility
US8426833B2 (en) 2006-05-12 2013-04-23 Brookhaven Science Associates, Llc Gantry for medical particle therapy facility
US8173981B2 (en) 2006-05-12 2012-05-08 Brookhaven Science Associates, Llc Gantry for medical particle therapy facility
US7466085B2 (en) 2007-04-17 2008-12-16 Advanced Biomarker Technologies, Llc Cyclotron having permanent magnets
US7476883B2 (en) 2006-05-26 2009-01-13 Advanced Biomarker Technologies, Llc Biomarker generator system
US7817836B2 (en) 2006-06-05 2010-10-19 Varian Medical Systems, Inc. Methods for volumetric contouring with expert guidance
US7402823B2 (en) 2006-06-05 2008-07-22 Varian Medical Systems Technologies, Inc. Particle beam system including exchangeable particle beam nozzle
JP5116996B2 (en) 2006-06-20 2013-01-09 キヤノン株式会社 Charged particle beam drawing method, exposure apparatus, and device manufacturing method
US7990524B2 (en) 2006-06-30 2011-08-02 The University Of Chicago Stochastic scanning apparatus using multiphoton multifocal source
JP4206414B2 (en) 2006-07-07 2009-01-14 株式会社日立製作所 Charged particle beam extraction apparatus and charged particle beam extraction method
EP2046450A4 (en) 2006-07-28 2009-10-21 Tomotherapy Inc Method and apparatus for calibrating a radiation therapy treatment system
DE102006035094B3 (en) 2006-07-28 2008-04-10 Siemens Ag Magnet e.g. deflection magnet, for use in e.g. gantry, has recondensation surfaces assigned to pipeline systems such that one of surfaces lies at geodesic height that is equal or greater than height of other surface during magnet rotation
JP4881677B2 (en) 2006-08-31 2012-02-22 株式会社日立ハイテクノロジーズ Charged particle beam scanning method and charged particle beam apparatus
JP4872540B2 (en) 2006-08-31 2012-02-08 株式会社日立製作所 Rotating irradiation treatment device
US7701677B2 (en) 2006-09-07 2010-04-20 Massachusetts Institute Of Technology Inductive quench for magnet protection
JP4365844B2 (en) 2006-09-08 2009-11-18 三菱電機株式会社 Charged particle beam dose distribution measurement system
EP2069702A1 (en) 2006-09-13 2009-06-17 ExxonMobil Chemical Patents Inc. Quench exchanger with extended surface on process side
US9451928B2 (en) * 2006-09-13 2016-09-27 Elekta Ltd. Incorporating internal anatomy in clinical radiotherapy setups
US7950587B2 (en) 2006-09-22 2011-05-31 The Board of Regents of the Nevada System of Higher Education on behalf of the University of Reno, Nevada Devices and methods for storing data
DE102006046688B3 (en) 2006-09-29 2008-01-24 Siemens Ag Cooling system, e.g. for super conductive magnets, gives a non-mechanical separation between the parts to be cooled and the heat sink
DE102006048426B3 (en) 2006-10-12 2008-05-21 Siemens Ag Method for determining the range of radiation
DE202006019307U1 (en) 2006-12-21 2008-04-24 Accel Instruments Gmbh irradiator
DE602006014454D1 (en) 2006-12-28 2010-07-01 Fond Per Adroterapia Oncologic ION ACCELERATION SYSTEM FOR MEDICAL AND / OR OTHER APPLICATIONS
JP4655046B2 (en) 2007-01-10 2011-03-23 三菱電機株式会社 Linear ion accelerator
FR2911843B1 (en) 2007-01-30 2009-04-10 Peugeot Citroen Automobiles Sa TRUCK SYSTEM FOR TRANSPORTING AND HANDLING BINS FOR SUPPLYING PARTS OF A VEHICLE MOUNTING LINE
JP4228018B2 (en) 2007-02-16 2009-02-25 三菱重工業株式会社 Medical equipment
JP4936924B2 (en) 2007-02-20 2012-05-23 稔 植松 Particle beam irradiation system
WO2008106483A1 (en) * 2007-02-27 2008-09-04 Wisconsin Alumni Research Foundation Ion radiation therapy system with distal gradient tracking
US7977648B2 (en) 2007-02-27 2011-07-12 Wisconsin Alumni Research Foundation Scanning aperture ion beam modulator
US8093568B2 (en) 2007-02-27 2012-01-10 Wisconsin Alumni Research Foundation Ion radiation therapy system with rocking gantry motion
US7397901B1 (en) 2007-02-28 2008-07-08 Varian Medical Systems Technologies, Inc. Multi-leaf collimator with leaves formed of different materials
US7778488B2 (en) 2007-03-23 2010-08-17 Varian Medical Systems International Ag Image deformation using multiple image regions
US7453076B2 (en) 2007-03-23 2008-11-18 Nanolife Sciences, Inc. Bi-polar treatment facility for treating target cells with both positive and negative ions
US8041006B2 (en) 2007-04-11 2011-10-18 The Invention Science Fund I Llc Aspects of compton scattered X-ray visualization, imaging, or information providing
DE102007020599A1 (en) 2007-05-02 2008-11-06 Siemens Ag Particle therapy system
DE102007021033B3 (en) 2007-05-04 2009-03-05 Siemens Ag Beam guiding magnet for deflecting a beam of electrically charged particles along a curved particle path and irradiation system with such a magnet
US7668291B2 (en) 2007-05-18 2010-02-23 Varian Medical Systems International Ag Leaf sequencing
JP5004659B2 (en) 2007-05-22 2012-08-22 株式会社日立ハイテクノロジーズ Charged particle beam equipment
US7947969B2 (en) 2007-06-27 2011-05-24 Mitsubishi Electric Corporation Stacked conformation radiotherapy system and particle beam therapy apparatus employing the same
DE102007036035A1 (en) 2007-08-01 2009-02-05 Siemens Ag Control device for controlling an irradiation process, particle therapy system and method for irradiating a target volume
US7770231B2 (en) 2007-08-02 2010-08-03 Veeco Instruments, Inc. Fast-scanning SPM and method of operating same
DE102007037406A1 (en) 2007-08-08 2009-06-04 Neoplas Gmbh Method and device for plasma assisted surface treatment
US20090038318A1 (en) 2007-08-10 2009-02-12 Telsa Engineering Ltd. Cooling methods
JP4339904B2 (en) 2007-08-17 2009-10-07 株式会社日立製作所 Particle beam therapy system
CN101815471A (en) 2007-09-04 2010-08-25 断层放疗公司 Patient support device and method of operation
DE102007042340C5 (en) 2007-09-06 2011-09-22 Mt Mechatronics Gmbh Particle therapy system with moveable C-arm
US7848488B2 (en) 2007-09-10 2010-12-07 Varian Medical Systems, Inc. Radiation systems having tiltable gantry
CN101903063B (en) 2007-09-12 2014-05-07 株式会社东芝 Particle beam projection apparatus
US7582866B2 (en) 2007-10-03 2009-09-01 Shimadzu Corporation Ion trap mass spectrometry
US8003964B2 (en) 2007-10-11 2011-08-23 Still River Systems Incorporated Applying a particle beam to a patient
DE102007050035B4 (en) 2007-10-17 2015-10-08 Siemens Aktiengesellschaft Apparatus and method for deflecting a jet of electrically charged particles onto a curved particle path
DE102007050168B3 (en) 2007-10-19 2009-04-30 Siemens Ag Gantry, particle therapy system and method for operating a gantry with a movable actuator
US8222616B2 (en) * 2007-10-25 2012-07-17 Tomotherapy Incorporated Method for adapting fractionation of a radiation therapy dose
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
US8581523B2 (en) 2007-11-30 2013-11-12 Mevion Medical Systems, Inc. Interrupted particle source
ES2547342T3 (en) 2007-11-30 2015-10-05 Mevion Medical Systems, Inc. Interior porch
CN103252024B (en) 2007-11-30 2016-02-10 梅维昂医疗系统股份有限公司 Particle beam therapy system
TWI448313B (en) 2007-11-30 2014-08-11 Mevion Medical Systems Inc System having an inner gantry
JP2009146934A (en) 2007-12-11 2009-07-02 Hitachi Ltd Cryostat for superconducting electromagnet
US8085899B2 (en) 2007-12-12 2011-12-27 Varian Medical Systems International Ag Treatment planning system and method for radiotherapy
ATE521979T1 (en) 2007-12-17 2011-09-15 Zeiss Carl Nts Gmbh RASTER SCANNING BEAMS OF CHARGED PARTICLES
CN101946180B (en) 2007-12-19 2013-11-13 神谷来克斯公司 Scanning analyzer for single molecule detection and methods of use
JP5074915B2 (en) 2007-12-21 2012-11-14 株式会社日立製作所 Charged particle beam irradiation system
DE102008005069B4 (en) 2008-01-18 2017-06-08 Siemens Healthcare Gmbh Positioning device for positioning a patient, particle therapy system and method for operating a positioning device
JP2009192244A (en) 2008-02-12 2009-08-27 Toyota Motor Corp Driving assisting system
DE102008014406A1 (en) 2008-03-14 2009-09-24 Siemens Aktiengesellschaft Particle therapy system and method for modulating a particle beam generated in an accelerator
US7919765B2 (en) 2008-03-20 2011-04-05 Varian Medical Systems Particle Therapy Gmbh Non-continuous particle beam irradiation method and apparatus
JP5107113B2 (en) 2008-03-28 2012-12-26 住友重機械工業株式会社 Charged particle beam irradiation equipment
JP5143606B2 (en) 2008-03-28 2013-02-13 住友重機械工業株式会社 Charged particle beam irradiation equipment
DE102008018417A1 (en) 2008-04-10 2009-10-29 Siemens Aktiengesellschaft Method and device for creating an irradiation plan
JP4719241B2 (en) 2008-04-15 2011-07-06 三菱電機株式会社 Circular accelerator
US7759642B2 (en) 2008-04-30 2010-07-20 Applied Materials Israel, Ltd. Pattern invariant focusing of a charged particle beam
JP4691574B2 (en) 2008-05-14 2011-06-01 株式会社日立製作所 Charged particle beam extraction apparatus and charged particle beam extraction method
US8309941B2 (en) 2008-05-22 2012-11-13 Vladimir Balakin Charged particle cancer therapy and patient breath monitoring method and apparatus
US8144832B2 (en) 2008-05-22 2012-03-27 Vladimir Balakin X-ray tomography method and apparatus used in conjunction with a charged particle cancer therapy system
US8368038B2 (en) 2008-05-22 2013-02-05 Vladimir Balakin Method and apparatus for intensity control of a charged particle beam extracted from a synchrotron
US8178859B2 (en) 2008-05-22 2012-05-15 Vladimir Balakin Proton beam positioning verification method and apparatus used in conjunction with a charged particle cancer therapy system
US8198607B2 (en) 2008-05-22 2012-06-12 Vladimir Balakin Tandem accelerator method and apparatus used in conjunction with a charged particle cancer therapy system
MX2010012716A (en) 2008-05-22 2011-07-01 Vladimir Yegorovich Balakin X-ray method and apparatus used in conjunction with a charged particle cancer therapy system.
US8288742B2 (en) 2008-05-22 2012-10-16 Vladimir Balakin Charged particle cancer therapy patient positioning method and apparatus
US8373145B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Charged particle cancer therapy system magnet control method and apparatus
US8129699B2 (en) 2008-05-22 2012-03-06 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus coordinated with patient respiration
US8399866B2 (en) 2008-05-22 2013-03-19 Vladimir Balakin Charged particle extraction apparatus and method of use thereof
US8093564B2 (en) 2008-05-22 2012-01-10 Vladimir Balakin Ion beam focusing lens method and apparatus used in conjunction with a charged particle cancer therapy system
US8188688B2 (en) 2008-05-22 2012-05-29 Vladimir Balakin Magnetic field control method and apparatus used in conjunction with a charged particle cancer therapy system
US8089054B2 (en) 2008-05-22 2012-01-03 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US7943913B2 (en) 2008-05-22 2011-05-17 Vladimir Balakin Negative ion source method and apparatus used in conjunction with a charged particle cancer therapy system
US8569717B2 (en) 2008-05-22 2013-10-29 Vladimir Balakin Intensity modulated three-dimensional radiation scanning method and apparatus
US8378321B2 (en) 2008-05-22 2013-02-19 Vladimir Balakin Charged particle cancer therapy and patient positioning method and apparatus
US7940894B2 (en) 2008-05-22 2011-05-10 Vladimir Balakin Elongated lifetime X-ray method and apparatus used in conjunction with a charged particle cancer therapy system
US8373143B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Patient immobilization and repositioning method and apparatus used in conjunction with charged particle cancer therapy
US7834336B2 (en) 2008-05-28 2010-11-16 Varian Medical Systems, Inc. Treatment of patient tumors by charged particle therapy
US7987053B2 (en) 2008-05-30 2011-07-26 Varian Medical Systems International Ag Monitor units calculation method for proton fields
US7801270B2 (en) 2008-06-19 2010-09-21 Varian Medical Systems International Ag Treatment plan optimization method for radiation therapy
DE102008029609A1 (en) 2008-06-23 2009-12-31 Siemens Aktiengesellschaft Device and method for measuring a beam spot of a particle beam and system for generating a particle beam
US8227768B2 (en) 2008-06-25 2012-07-24 Axcelis Technologies, Inc. Low-inertia multi-axis multi-directional mechanically scanned ion implantation system
US7809107B2 (en) 2008-06-30 2010-10-05 Varian Medical Systems International Ag Method for controlling modulation strength in radiation therapy
DE102008033467B4 (en) 2008-07-16 2010-04-08 Siemens Aktiengesellschaft Cryostat for superconducting MR magnets
JP4691587B2 (en) 2008-08-06 2011-06-01 三菱重工業株式会社 Radiotherapy apparatus and radiation irradiation method
US7796731B2 (en) 2008-08-22 2010-09-14 Varian Medical Systems International Ag Leaf sequencing algorithm for moving targets
US8330132B2 (en) 2008-08-27 2012-12-11 Varian Medical Systems, Inc. Energy modulator for modulating an energy of a particle beam
US7835494B2 (en) 2008-08-28 2010-11-16 Varian Medical Systems International Ag Trajectory optimization method
US7817778B2 (en) 2008-08-29 2010-10-19 Varian Medical Systems International Ag Interactive treatment plan optimization for radiation therapy
US8334520B2 (en) 2008-10-24 2012-12-18 Hitachi High-Technologies Corporation Charged particle beam apparatus
US7609811B1 (en) 2008-11-07 2009-10-27 Varian Medical Systems International Ag Method for minimizing the tongue and groove effect in intensity modulated radiation delivery
US7839973B2 (en) 2009-01-14 2010-11-23 Varian Medical Systems International Ag Treatment planning using modulability and visibility factors
JP5292412B2 (en) 2009-01-15 2013-09-18 株式会社日立ハイテクノロジーズ Charged particle beam application equipment
GB2467595B (en) 2009-02-09 2011-08-24 Tesla Engineering Ltd Cooling systems and methods
US7835502B2 (en) 2009-02-11 2010-11-16 Tomotherapy Incorporated Target pedestal assembly and method of preserving the target
US7986768B2 (en) 2009-02-19 2011-07-26 Varian Medical Systems International Ag Apparatus and method to facilitate generating a treatment plan for irradiating a patient's treatment volume
US8053745B2 (en) 2009-02-24 2011-11-08 Moore John F Device and method for administering particle beam therapy
US8063381B2 (en) * 2009-03-13 2011-11-22 Brookhaven Science Associates, Llc Achromatic and uncoupled medical gantry
US8238988B2 (en) 2009-03-31 2012-08-07 General Electric Company Apparatus and method for cooling a superconducting magnetic assembly
US8257649B2 (en) * 2009-04-27 2012-09-04 Hgi Industries, Inc. Hydroxyl generator
US7934869B2 (en) 2009-06-30 2011-05-03 Mitsubishi Electric Research Labs, Inc. Positioning an object based on aligned images of the object
US7894574B1 (en) 2009-09-22 2011-02-22 Varian Medical Systems International Ag Apparatus and method pertaining to dynamic use of a radiation therapy collimator
DK2308561T3 (en) * 2009-09-28 2011-10-03 Ion Beam Applic Compact gantry for particle therapy
US8009803B2 (en) 2009-09-28 2011-08-30 Varian Medical Systems International Ag Treatment plan optimization method for radiosurgery
US8009804B2 (en) 2009-10-20 2011-08-30 Varian Medical Systems International Ag Dose calculation method for multiple fields
US8382943B2 (en) 2009-10-23 2013-02-26 William George Clark Method and apparatus for the selective separation of two layers of material using an ultrashort pulse source of electromagnetic radiation
WO2011092815A1 (en) 2010-01-28 2011-08-04 三菱電機株式会社 Particle beam treatment apparatus
JP5463509B2 (en) 2010-02-10 2014-04-09 株式会社東芝 Particle beam irradiation apparatus and control method thereof
JP2011182987A (en) 2010-03-09 2011-09-22 Sumitomo Heavy Ind Ltd Accelerated particle irradiation equipment
EP2365514B1 (en) 2010-03-10 2015-08-26 ICT Integrated Circuit Testing Gesellschaft für Halbleiterprüftechnik mbH Twin beam charged particle column and method of operating thereof
US9234691B2 (en) 2010-03-11 2016-01-12 Quantum Design International, Inc. Method and apparatus for controlling temperature in a cryocooled cryostat using static and moving gas
EP2579265B1 (en) 2010-05-27 2015-12-02 Mitsubishi Electric Corporation Particle beam irradiation system
JPWO2012014705A1 (en) 2010-07-28 2013-09-12 住友重機械工業株式会社 Charged particle beam irradiation equipment
US8416918B2 (en) 2010-08-20 2013-04-09 Varian Medical Systems International Ag Apparatus and method pertaining to radiation-treatment planning optimization
JP5670126B2 (en) 2010-08-26 2015-02-18 住友重機械工業株式会社 Charged particle beam irradiation apparatus, charged particle beam irradiation method, and charged particle beam irradiation program
US8445872B2 (en) 2010-09-03 2013-05-21 Varian Medical Systems Particle Therapy Gmbh System and method for layer-wise proton beam current variation
US8472583B2 (en) 2010-09-29 2013-06-25 Varian Medical Systems, Inc. Radiation scanning of objects for contraband
US8374663B2 (en) 2011-01-31 2013-02-12 General Electric Company Cooling system and method for cooling superconducting magnet devices
EP2845623B1 (en) 2011-02-17 2016-12-21 Mitsubishi Electric Corporation Particle beam therapy system
JP5744578B2 (en) * 2011-03-10 2015-07-08 住友重機械工業株式会社 Charged particle beam irradiation system and neutron beam irradiation system
US8653314B2 (en) 2011-05-22 2014-02-18 Fina Technology, Inc. Method for providing a co-feed in the coupling of toluene with a carbon source
EP2637181B1 (en) 2012-03-06 2018-05-02 Tesla Engineering Limited Multi orientation cryostats
US8581525B2 (en) 2012-03-23 2013-11-12 Massachusetts Institute Of Technology Compensated precessional beam extraction for cyclotrons
JP6121546B2 (en) * 2012-09-28 2017-04-26 メビオン・メディカル・システムズ・インコーポレーテッド Control system for particle accelerator
JP6121544B2 (en) * 2012-09-28 2017-04-26 メビオン・メディカル・システムズ・インコーポレーテッド Particle beam focusing
US10254739B2 (en) * 2012-09-28 2019-04-09 Mevion Medical Systems, Inc. Coil positioning system
EP2901824B1 (en) * 2012-09-28 2020-04-15 Mevion Medical Systems, Inc. Magnetic shims to adjust a position of a main coil and corresponding method
JP6367201B2 (en) * 2012-09-28 2018-08-01 メビオン・メディカル・システムズ・インコーポレーテッド Control of particle beam intensity
CN104813747B (en) * 2012-09-28 2018-02-02 梅维昂医疗系统股份有限公司 Use magnetic field flutter focused particle beam
EP3581242B1 (en) * 2012-09-28 2022-04-06 Mevion Medical Systems, Inc. Adjusting energy of a particle beam
WO2014052734A1 (en) * 2012-09-28 2014-04-03 Mevion Medical Systems, Inc. Controlling particle therapy
CN108770178B (en) * 2012-09-28 2021-04-16 迈胜医疗设备有限公司 Magnetic field regenerator
GB201217782D0 (en) 2012-10-04 2012-11-14 Tesla Engineering Ltd Magnet apparatus
JP5662502B2 (en) 2013-03-07 2015-01-28 メビオン・メディカル・システムズ・インコーポレーテッド Inner gantry
JP5662503B2 (en) 2013-03-07 2015-01-28 メビオン・メディカル・システムズ・インコーポレーテッド Inner gantry
US8791656B1 (en) * 2013-05-31 2014-07-29 Mevion Medical Systems, Inc. Active return system
JP6180800B2 (en) 2013-06-06 2017-08-16 サッポロビール株式会社 Packing box and package
US9730308B2 (en) * 2013-06-12 2017-08-08 Mevion Medical Systems, Inc. Particle accelerator that produces charged particles having variable energies
CN110237447B (en) * 2013-09-27 2021-11-02 梅维昂医疗系统股份有限公司 Particle therapy system
GB2519595B (en) * 2013-10-28 2015-09-23 Elekta Ab Image guided radiation therapy apparatus
US9962560B2 (en) * 2013-12-20 2018-05-08 Mevion Medical Systems, Inc. Collimator and energy degrader
US9661736B2 (en) * 2014-02-20 2017-05-23 Mevion Medical Systems, Inc. Scanning system for a particle therapy system
US9950194B2 (en) * 2014-09-09 2018-04-24 Mevion Medical Systems, Inc. Patient positioning system
SG10202101289RA (en) 2015-03-24 2021-03-30 Kla Tencor Corp Method and system for charged particle microscopy with improved image beam stabilization and interrogation

Patent Citations (99)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2280606A (en) * 1940-01-26 1942-04-21 Rca Corp Electronic reactance circuits
US3582650A (en) * 1960-08-01 1971-06-01 Varian Associates Support structure for electron accelerator with deflecting means and target and cooperating patient support
US3757118A (en) * 1972-02-22 1973-09-04 Ca Atomic Energy Ltd Electron beam therapy unit
US3886367A (en) * 1974-01-18 1975-05-27 Us Energy Ion-beam mask for cancer patient therapy
US3955089A (en) * 1974-10-21 1976-05-04 Varian Associates Automatic steering of a high velocity beam of charged particles
US4139777A (en) * 1975-11-19 1979-02-13 Rautenbach Willem L Cyclotron and neutron therapy installation incorporating such a cyclotron
US4112306A (en) * 1976-12-06 1978-09-05 Varian Associates, Inc. Neutron irradiation therapy machine
US4220866A (en) * 1977-12-30 1980-09-02 Siemens Aktiengesellschaft Electron applicator
US4197510A (en) * 1978-06-23 1980-04-08 The United States Of America As Represented By The Secretary Of The Navy Isochronous cyclotron
US4345210A (en) * 1979-05-31 1982-08-17 C.G.R. Mev Microwave resonant system with dual resonant frequency and a cyclotron fitted with such a system
US4256966A (en) * 1979-07-03 1981-03-17 Siemens Medical Laboratories, Inc. Radiotherapy apparatus with two light beam localizers
US4336505A (en) * 1980-07-14 1982-06-22 John Fluke Mfg. Co., Inc. Controlled frequency signal source apparatus including a feedback path for the reduction of phase noise
US4425506A (en) * 1981-11-19 1984-01-10 Varian Associates, Inc. Stepped gap achromatic bending magnet
US4507616A (en) * 1982-03-08 1985-03-26 Board Of Trustees Operating Michigan State University Rotatable superconducting cyclotron adapted for medical use
US4598208A (en) * 1982-10-04 1986-07-01 Varian Associates, Inc. Collimation system for electron arc therapy
US4507614A (en) * 1983-03-21 1985-03-26 The United States Of America As Represented By The United States Department Of Energy Electrostatic wire for stabilizing a charged particle beam
US4736173A (en) * 1983-06-30 1988-04-05 Hughes Aircraft Company Thermally-compensated microwave resonator utilizing current-null segmentation
US4589126A (en) * 1984-01-26 1986-05-13 Augustsson Nils E Radiotherapy treatment table
US4865284A (en) * 1984-03-13 1989-09-12 Siemens Gammasonics, Inc. Collimator storage device in particular a collimator cart
US4641104A (en) * 1984-04-26 1987-02-03 Board Of Trustees Operating Michigan State University Superconducting medical cyclotron
US4904949A (en) * 1984-08-28 1990-02-27 Oxford Instruments Limited Synchrotron with superconducting coils and arrangement thereof
US4651007A (en) * 1984-09-13 1987-03-17 Technicare Corporation Medical diagnostic mechanical positioner
US4641057A (en) * 1985-01-23 1987-02-03 Board Of Trustees Operating Michigan State University Superconducting synchrocyclotron
US4734653A (en) * 1985-02-25 1988-03-29 Siemens Aktiengesellschaft Magnetic field apparatus for a particle accelerator having a supplemental winding with a hollow groove structure
US4745367A (en) * 1985-03-28 1988-05-17 Kernforschungszentrum Karlsruhe Gmbh Superconducting magnet system for particle accelerators of a synchrotron radiation source
US4771208A (en) * 1985-05-10 1988-09-13 Yves Jongen Cyclotron
US4943781A (en) * 1985-05-21 1990-07-24 Oxford Instruments, Ltd. Cyclotron with yokeless superconducting magnet
US4680565A (en) * 1985-06-24 1987-07-14 Siemens Aktiengesellschaft Magnetic field device for a system for the acceleration and/or storage of electrically charged particles
US4726046A (en) * 1985-11-05 1988-02-16 Varian Associates, Inc. X-ray and electron radiotherapy clinical treatment machine
US4737727A (en) * 1986-02-12 1988-04-12 Mitsubishi Denki Kabushiki Kaisha Charged beam apparatus
US4754147A (en) * 1986-04-11 1988-06-28 Michigan State University Variable radiation collimator
US4868843A (en) * 1986-09-10 1989-09-19 Varian Associates, Inc. Multileaf collimator and compensator for radiotherapy machines
US4868844A (en) * 1986-09-10 1989-09-19 Varian Associates, Inc. Mutileaf collimator for radiotherapy machines
US4808941A (en) * 1986-10-29 1989-02-28 Siemens Aktiengesellschaft Synchrotron with radiation absorber
US4843333A (en) * 1987-01-28 1989-06-27 Siemens Aktiengesellschaft Synchrotron radiation source having adjustable fixed curved coil windings
US4769623A (en) * 1987-01-28 1988-09-06 Siemens Aktiengesellschaft Magnetic device with curved superconducting coil windings
US4902993A (en) * 1987-02-19 1990-02-20 Kernforschungszentrum Karlsruhe Gmbh Magnetic deflection system for charged particles
US4812658A (en) * 1987-07-23 1989-03-14 President And Fellows Of Harvard College Beam Redirecting
US5039867A (en) * 1987-08-24 1991-08-13 Mitsubishi Denki Kabushiki Kaisha Therapeutic apparatus
US4996496A (en) * 1987-09-11 1991-02-26 Hitachi, Ltd. Bending magnet
US5189687A (en) * 1987-12-03 1993-02-23 University Of Florida Research Foundation, Inc. Apparatus for stereotactic radiosurgery
US4917344A (en) * 1988-04-07 1990-04-17 Loma Linda University Medical Center Roller-supported, modular, isocentric gantry and method of assembly
US5039057A (en) * 1988-04-07 1991-08-13 Loma Linda University Medical Center Roller-supported, modular, isocentric gentry and method of assembly
US4905267A (en) * 1988-04-29 1990-02-27 Loma Linda University Medical Center Method of assembly and whole body, patient positioning and repositioning support for use in radiation beam therapy systems
US5117194A (en) * 1988-08-26 1992-05-26 Mitsubishi Denki Kabushiki Kaisha Device for accelerating and storing charged particles
US5017882A (en) * 1988-09-01 1991-05-21 Amersham International Plc Proton source
US4987309A (en) * 1988-11-29 1991-01-22 Varian Associates, Inc. Radiation therapy unit
US5117212A (en) * 1989-01-12 1992-05-26 Mitsubishi Denki Kabushiki Kaisha Electromagnet for charged-particle apparatus
US5036290A (en) * 1989-03-15 1991-07-30 Hitachi, Ltd. Synchrotron radiation generation apparatus
US5117829A (en) * 1989-03-31 1992-06-02 Loma Linda University Medical Center Patient alignment system and procedure for radiation treatment
US5017789A (en) * 1989-03-31 1991-05-21 Loma Linda University Medical Center Raster scan control system for a charged-particle beam
US5111173A (en) * 1990-03-27 1992-05-05 Mitsubishi Denki Kabushiki Kaisha Deflection electromagnet for a charged particle device
US5341104A (en) * 1990-08-06 1994-08-23 Siemens Aktiengesellschaft Synchrotron radiation source
US5278533A (en) * 1990-08-31 1994-01-11 Mitsubishi Denki Kabushiki Kaisha Coil for use in charged particle deflecting electromagnet and method of manufacturing the same
US5317164A (en) * 1991-06-12 1994-05-31 Mitsubishi Denki Kabushiki Kaisha Radiotherapy device
US5405235A (en) * 1991-07-26 1995-04-11 Lebre; Charles J. P. Barrel grasping device for automatically clamping onto the pole of a barrel trolley
US5240218A (en) * 1991-10-23 1993-08-31 Loma Linda University Medical Center Retractable support assembly
US5521469A (en) * 1991-11-22 1996-05-28 Laisne; Andre E. P. Compact isochronal cyclotron
US5382914A (en) * 1992-05-05 1995-01-17 Accsys Technology, Inc. Proton-beam therapy linac
US5336891A (en) * 1992-06-16 1994-08-09 Arch Development Corporation Aberration free lens system for electron microscope
US5401973A (en) * 1992-12-04 1995-03-28 Atomic Energy Of Canada Limited Industrial material processing electron linear accelerator
US5434420A (en) * 1992-12-04 1995-07-18 Atomic Energy Of Canada Limited Industrial material processing electron linear accelerator
US5440133A (en) * 1993-07-02 1995-08-08 Loma Linda University Medical Center Charged particle beam scattering system
US5511549A (en) * 1995-02-13 1996-04-30 Loma Linda Medical Center Normalizing and calibrating therapeutic radiation delivery systems
US5751781A (en) * 1995-10-07 1998-05-12 Elekta Ab Apparatus for treating a patient
US5726448A (en) * 1996-08-09 1998-03-10 California Institute Of Technology Rotating field mass and velocity analyzer
US5778047A (en) * 1996-10-24 1998-07-07 Varian Associates, Inc. Radiotherapy couch top
US6683318B1 (en) * 1998-09-11 2004-01-27 Gesellschaft Fuer Schwerionenforschung Mbh Ion beam therapy system and a method for operating the system
US6600164B1 (en) * 1999-02-19 2003-07-29 Gesellschaft Fuer Schwerionenforschung Mbh Method of operating an ion beam therapy system with monitoring of beam position
US6736831B1 (en) * 1999-02-19 2004-05-18 Gesellschaft Fuer Schwerionenforschung Mbh Method for operating an ion beam therapy system by monitoring the distribution of the radiation dose
US6745072B1 (en) * 1999-02-19 2004-06-01 Gesellschaft Fuer Schwerionenforschung Mbh Method for checking beam generation and beam acceleration means of an ion beam therapy system
US7318805B2 (en) * 1999-03-16 2008-01-15 Accuray Incorporated Apparatus and method for compensating for respiratory and patient motion during treatment
US20030125622A1 (en) * 1999-03-16 2003-07-03 Achim Schweikard Apparatus and method for compensating for respiratory and patient motion during treatment
US20030136924A1 (en) * 2000-06-30 2003-07-24 Gerhard Kraft Device for irradiating a tumor tissue
US6710362B2 (en) * 2000-06-30 2004-03-23 Gesellschaft Fuer Schwerionenforschung Mbh Device for irradiating a tumor tissue
US6407505B1 (en) * 2001-02-01 2002-06-18 Siemens Medical Solutions Usa, Inc. Variable energy linear accelerator
US6853703B2 (en) * 2001-07-20 2005-02-08 Siemens Medical Solutions Usa, Inc. Automated delivery of treatment fields
US6519316B1 (en) * 2001-11-02 2003-02-11 Siemens Medical Solutions Usa, Inc.. Integrated control of portal imaging device
US6777689B2 (en) * 2001-11-16 2004-08-17 Ion Beam Application, S.A. Article irradiation system shielding
US6993112B2 (en) * 2002-03-12 2006-01-31 Deutsches Krebsforschungszentrum Stiftung Des Oeffentlichen Rechts Device for performing and verifying a therapeutic treatment and corresponding computer program and control method
US7008105B2 (en) * 2002-05-13 2006-03-07 Siemens Aktiengesellschaft Patient support device for radiation therapy
US6865254B2 (en) * 2002-07-02 2005-03-08 Pencilbeam Technologies Ab Radiation system with inner and outer gantry parts
US20040017888A1 (en) * 2002-07-24 2004-01-29 Seppi Edward J. Radiation scanning of objects for contraband
US6897451B2 (en) * 2002-09-05 2005-05-24 Man Technologie Ag Isokinetic gantry arrangement for the isocentric guidance of a particle beam and a method for constructing same
US20040159795A1 (en) * 2002-09-05 2004-08-19 Man Technologie Ag Isokinetic gantry arrangement for the isocentric guidance of a particle beam and a method for constructing same
US7348579B2 (en) * 2002-09-18 2008-03-25 Paul Scherrer Institut Arrangement for performing proton therapy
US6984835B2 (en) * 2003-04-23 2006-01-10 Mitsubishi Denki Kabushiki Kaisha Irradiation apparatus and irradiation method
US20060145088A1 (en) * 2003-06-02 2006-07-06 Fox Chase Cancer Center High energy polyenergetic ion selection systems, ion beam therapy systems, and ion beam treatment centers
US20050058245A1 (en) * 2003-09-11 2005-03-17 Moshe Ein-Gal Intensity-modulated radiation therapy with a multilayer multileaf collimator
US7208748B2 (en) * 2004-07-21 2007-04-24 Still River Systems, Inc. Programmable particle scatterer for radiation therapy beam formation
US20060017015A1 (en) * 2004-07-21 2006-01-26 Still River Systems, Inc. Programmable particle scatterer for radiation therapy beam formation
US20060067468A1 (en) * 2004-09-30 2006-03-30 Eike Rietzel Radiotherapy systems
US20070029510A1 (en) * 2005-08-05 2007-02-08 Siemens Aktiengesellschaft Gantry system for a particle therapy facility
US7208745B2 (en) * 2005-08-18 2007-04-24 Konica Minolta Medical & Graphic, Inc. Radiation image conversion panel
US20070051904A1 (en) * 2005-08-30 2007-03-08 Werner Kaiser Gantry system for particle therapy, therapy plan or radiation method for particle therapy with such a gantry system
US20070171015A1 (en) * 2006-01-19 2007-07-26 Massachusetts Institute Of Technology High-Field Superconducting Synchrocyclotron
US7541905B2 (en) * 2006-01-19 2009-06-02 Massachusetts Institute Of Technology High-field superconducting synchrocyclotron
US7656258B1 (en) * 2006-01-19 2010-02-02 Massachusetts Institute Of Technology Magnet structure for particle acceleration
US7696847B2 (en) * 2006-01-19 2010-04-13 Massachusetts Institute Of Technology High-field synchrocyclotron

Cited By (157)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
USRE48047E1 (en) 2004-07-21 2020-06-09 Mevion Medical Systems, Inc. Programmable radio frequency waveform generator for a synchrocyclotron
US20110133699A1 (en) * 2004-10-29 2011-06-09 Medtronic, Inc. Lithium-ion battery
US10722735B2 (en) 2005-11-18 2020-07-28 Mevion Medical Systems, Inc. Inner gantry
US10279199B2 (en) * 2005-11-18 2019-05-07 Mevion Medical Systems, Inc. Inner gantry
US9925395B2 (en) 2005-11-18 2018-03-27 Mevion Medical Systems, Inc. Inner gantry
US9452301B2 (en) 2005-11-18 2016-09-27 Mevion Medical Systems, Inc. Inner gantry
US8581523B2 (en) 2007-11-30 2013-11-12 Mevion Medical Systems, Inc. Interrupted particle source
USRE48317E1 (en) 2007-11-30 2020-11-17 Mevion Medical Systems, Inc. Interrupted particle source
US8970137B2 (en) 2007-11-30 2015-03-03 Mevion Medical Systems, Inc. Interrupted particle source
US9168392B1 (en) 2008-05-22 2015-10-27 Vladimir Balakin Charged particle cancer therapy system X-ray apparatus and method of use thereof
US20100266100A1 (en) * 2008-05-22 2010-10-21 Dr. Vladimir Balakin Charged particle cancer therapy beam path control method and apparatus
US8093564B2 (en) 2008-05-22 2012-01-10 Vladimir Balakin Ion beam focusing lens method and apparatus used in conjunction with a charged particle cancer therapy system
US8129694B2 (en) 2008-05-22 2012-03-06 Vladimir Balakin Negative ion beam source vacuum method and apparatus used in conjunction with a charged particle cancer therapy system
US8129699B2 (en) 2008-05-22 2012-03-06 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus coordinated with patient respiration
US8144832B2 (en) 2008-05-22 2012-03-27 Vladimir Balakin X-ray tomography method and apparatus used in conjunction with a charged particle cancer therapy system
US8178859B2 (en) 2008-05-22 2012-05-15 Vladimir Balakin Proton beam positioning verification method and apparatus used in conjunction with a charged particle cancer therapy system
US8188688B2 (en) 2008-05-22 2012-05-29 Vladimir Balakin Magnetic field control method and apparatus used in conjunction with a charged particle cancer therapy system
US20120143051A1 (en) * 2008-05-22 2012-06-07 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus coordinated with patient respiration
US8198607B2 (en) 2008-05-22 2012-06-12 Vladimir Balakin Tandem accelerator method and apparatus used in conjunction with a charged particle cancer therapy system
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US8941084B2 (en) 2008-05-22 2015-01-27 Vladimir Balakin Charged particle cancer therapy dose distribution method and apparatus
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US10518109B2 (en) 2010-04-16 2019-12-31 Jillian Reno Transformable charged particle beam path cancer therapy apparatus and method of use thereof
US10751551B2 (en) 2010-04-16 2020-08-25 James P. Bennett Integrated imaging-cancer treatment apparatus and method of use thereof
US10556126B2 (en) 2010-04-16 2020-02-11 Mark R. Amato Automated radiation treatment plan development apparatus and method of use thereof
US10589128B2 (en) 2010-04-16 2020-03-17 Susan L. Michaud Treatment beam path verification in a cancer therapy apparatus and method of use thereof
US10376717B2 (en) 2010-04-16 2019-08-13 James P. Bennett Intervening object compensating automated radiation treatment plan development apparatus and method of use thereof
US10357666B2 (en) 2010-04-16 2019-07-23 W. Davis Lee Fiducial marker / cancer imaging and treatment apparatus and method of use thereof
US10349906B2 (en) 2010-04-16 2019-07-16 James P. Bennett Multiplexed proton tomography imaging apparatus and method of use thereof
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US10029124B2 (en) 2010-04-16 2018-07-24 W. Davis Lee Multiple beamline position isocenterless positively charged particle cancer therapy apparatus and method of use thereof
US10638988B2 (en) 2010-04-16 2020-05-05 Scott Penfold Simultaneous/single patient position X-ray and proton imaging apparatus and method of use thereof
US10555710B2 (en) 2010-04-16 2020-02-11 James P. Bennett Simultaneous multi-axes imaging apparatus and method of use thereof
US20130184512A1 (en) * 2010-07-28 2013-07-18 Sumitomo Heavy Industries, Ltd. Charged particle beam irradiation device
US8653473B2 (en) * 2010-07-28 2014-02-18 Sumitomo Heavy Industries, Ltd. Charged particle beam irradiation device
US8963112B1 (en) 2011-05-25 2015-02-24 Vladimir Balakin Charged particle cancer therapy patient positioning method and apparatus
WO2014018876A1 (en) 2012-07-27 2014-01-30 Massachusetts Institute Of Technology Ultra-light, magnetically shielded, high-current, compact cyclotron
US20170231081A1 (en) * 2012-09-28 2017-08-10 Mevion Medical Systems, Inc. Magnetic field regenerator
US9723705B2 (en) 2012-09-28 2017-08-01 Mevion Medical Systems, Inc. Controlling intensity of a particle beam
US10254739B2 (en) 2012-09-28 2019-04-09 Mevion Medical Systems, Inc. Coil positioning system
US9301384B2 (en) 2012-09-28 2016-03-29 Mevion Medical Systems, Inc. Adjusting energy of a particle beam
US9706636B2 (en) 2012-09-28 2017-07-11 Mevion Medical Systems, Inc. Adjusting energy of a particle beam
US20140094640A1 (en) * 2012-09-28 2014-04-03 Mevion Medical Systems, Inc. Magnetic Field Regenerator
US9185789B2 (en) 2012-09-28 2015-11-10 Mevion Medical Systems, Inc. Magnetic shims to alter magnetic fields
US10368429B2 (en) * 2012-09-28 2019-07-30 Mevion Medical Systems, Inc. Magnetic field regenerator
US9622335B2 (en) * 2012-09-28 2017-04-11 Mevion Medical Systems, Inc. Magnetic field regenerator
US9681531B2 (en) 2012-09-28 2017-06-13 Mevion Medical Systems, Inc. Control system for a particle accelerator
US9545528B2 (en) 2012-09-28 2017-01-17 Mevion Medical Systems, Inc. Controlling particle therapy
US10155124B2 (en) 2012-09-28 2018-12-18 Mevion Medical Systems, Inc. Controlling particle therapy
US9155186B2 (en) 2012-09-28 2015-10-06 Mevion Medical Systems, Inc. Focusing a particle beam using magnetic field flutter
US8933651B2 (en) 2012-11-16 2015-01-13 Vladimir Balakin Charged particle accelerator magnet apparatus and method of use thereof
US8791656B1 (en) 2013-05-31 2014-07-29 Mevion Medical Systems, Inc. Active return system
US9730308B2 (en) * 2013-06-12 2017-08-08 Mevion Medical Systems, Inc. Particle accelerator that produces charged particles having variable energies
US10258810B2 (en) 2013-09-27 2019-04-16 Mevion Medical Systems, Inc. Particle beam scanning
US10456591B2 (en) 2013-09-27 2019-10-29 Mevion Medical Systems, Inc. Particle beam scanning
US9962560B2 (en) 2013-12-20 2018-05-08 Mevion Medical Systems, Inc. Collimator and energy degrader
US10675487B2 (en) 2013-12-20 2020-06-09 Mevion Medical Systems, Inc. Energy degrader enabling high-speed energy switching
US10434331B2 (en) 2014-02-20 2019-10-08 Mevion Medical Systems, Inc. Scanning system
US9661736B2 (en) 2014-02-20 2017-05-23 Mevion Medical Systems, Inc. Scanning system for a particle therapy system
US9950194B2 (en) 2014-09-09 2018-04-24 Mevion Medical Systems, Inc. Patient positioning system
US11213697B2 (en) 2015-11-10 2022-01-04 Mevion Medical Systems, Inc. Adaptive aperture
US10646728B2 (en) 2015-11-10 2020-05-12 Mevion Medical Systems, Inc. Adaptive aperture
US10786689B2 (en) 2015-11-10 2020-09-29 Mevion Medical Systems, Inc. Adaptive aperture
US11786754B2 (en) 2015-11-10 2023-10-17 Mevion Medical Systems, Inc. Adaptive aperture
US9907981B2 (en) 2016-03-07 2018-03-06 Susan L. Michaud Charged particle translation slide control apparatus and method of use thereof
US10037863B2 (en) 2016-05-27 2018-07-31 Mark R. Amato Continuous ion beam kinetic energy dissipater apparatus and method of use thereof
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
US10653892B2 (en) 2017-06-30 2020-05-19 Mevion Medical Systems, Inc. Configurable collimator controlled using linear motors
US11291861B2 (en) 2019-03-08 2022-04-05 Mevion Medical Systems, Inc. Delivery of radiation by column and generating a treatment plan therefor
US11311746B2 (en) 2019-03-08 2022-04-26 Mevion Medical Systems, Inc. Collimator and energy degrader for a particle therapy system

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