Charged particle cancer therapy system magnet control method and apparatus

• US 8,373,145 B2
• Filed: 08/17/2009
• Issued: 02/12/2013
• Est. Priority Date: 05/22/2008
• Status: Active Grant

• Current Assignee: Andrey Vladimirovich Balakin, Pavel Vladimirovich Balakin
• Original Assignee: Vladimir Balakin
• Inventors: Balakin, Vladimir
• Primary Examiner(s): MASKELL, MICHAEL P
• Application Number:
  US12/542,155
• Publication Number:
  US 20100207552A1
• Time in Patent Office: 1,275 Days
• Field of Search: 250/396.R, 250/492.1, 250/492.3, 313/62, 315/503, 315/504
• US Class Current: 250/492.3
• CPC Class Codes: A61N 2005/1087 Ions; Protons
• CPC Class Codes: A61N 5/10 X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy A61N5/01 takes precedence
• CPC Class Codes: H05H 13/04 Synchrotrons
• CPC Class Codes: H05H 7/10 Arrangements for ejecting particles from orbits

Abstract

The invention comprises a charged particle beam acceleration, extraction, and/or targeting method and apparatus used in conjunction with charged particle beam radiation therapy of cancerous tumors. Novel design features of a synchrotron are described. Particularly, turning magnets, edge focusing magnets, concentrating magnetic field magnets, winding and control coils, and extraction elements are described that minimize the overall size of the synchrotron, provide a tightly controlled proton beam, directly reduce the size of required magnetic fields, directly reduces required operating power, and allow continual acceleration of protons in a synchrotron even during a process of extracting protons from the synchrotron.

Claims

1. A particle beam irradiation apparatus for cancer therapy of a tumor of a patient, said apparatus controlling an operational magnetic field, wherein the operational magnetic field controls direction of charged particles, said apparatus comprising:

a synchrotron comprising turning magnets, a magnetic field sensor, a gap through which the charged particles pass during use, and at least one correction coil, said magnetic field sensor placed proximate said gap in said synchrotron,

wherein, said turning magnets comprise;

windings operating at a first power level to generate a first magnetic field about said gap; and

said at least one correction coil operating at a second power level, said second power level less than about five percent of said first power level, to generate a correction magnetic field about said gap during use,

wherein the first magnetic field and the correction magnetic field combine to yield the operational magnetic field during use,

wherein said synchrotron adjusts to a target magnetic field strength via monitoring the operational magnetic field to determine said second power level, wherein as a result of lower power consumption said second power level allows for more accurate and/or precise control of the operational magnetic field.

2. The apparatus of claim 1, further comprising a feedback loop, said feedback loop using a signal from said magnetic field sensor to adjust said second power level to obtain the target magnetic field strength, wherein the target magnetic field strength is achieved by monitoring the operational magnetic field with said magnetic field sensor, wherein the target magnetic field strength is not achieved by stabilizing current applied to said windings.

3. The apparatus of claim 1, wherein the target magnetic field strength is continuously adjustable during x-axis and y-axis scanning of the charged particles in targeting the tumor during operation.

4. The apparatus of claim 3, wherein said second power level controlling said correction coil operates at less than two percent of said first power level applied to said windings of said turning magnets.

5. The apparatus of claim 1, wherein a single correction coil of said at least one correction coil wraps around at least two of said turning magnets in said synchrotron.

6. The apparatus of claim 1, wherein said synchrotron further comprises:

a focal system focusing the charged particles to a volume of less than about two millimeters in diameter; and

an active scanning system, wherein said active scanning system delivers the charged particles to said volume while simultaneously scanning position of said volume along all of;

a horizontal axis;

a vertical axis; and

a kinetic energy axis.

7. The apparatus of claim 1, wherein said gap comprises an entrance surface through which said operational magnetic field enters, said entrance surface comprising a surface polish of less than about five microns roughness.

8. The apparatus of claim 7, wherein said gap comprises dimensions of about two centimeters by about five centimeters.

9. The apparatus of claim 1, wherein at least one of said turning magnets comprises a core, wherein a gap surface cross-section distance of said core comprises a dimension of about five centimeters, wherein a core body cross-section distance of said core running parallel to said gap surface cross-section distance comprises a distance at least one and a half times said surface cross-section distance, wherein the resultant operational magnetic field at said gap surface cross-section distance results from a lesser magnetic field at said core body cross-section distance.

10. The apparatus of claim 1, wherein at least one of said turning magnets comprises a core wrapped by said at least one correction coil, said gap running through said core, wherein said core expands from an outer dimension of said gap with an angle of about twenty to sixty degrees, wherein the magnetic field concentrates in said core upon approach to said gap.

11. A method for adjusting an operational magnetic filed of a synchrotron for irradiation of a tumor of a patient with charged particles, wherein the operational magnetic field controls direction of the charged particles, said method comprising the steps of:

accelerating the charged particles with a synchrotron, said synchrotron comprising turning magnets, a magnetic field sensor, a gap through which the charged particles pass during use, and at least one correction coil, said magnetic field sensor placed proximate said gap in said synchrotron;

operating windings of said turning magnets at a first power level to generate a first magnetic field about said gap; and

generating a correction magnetic field with at least one correction coil operating at a second power level, said second power level less than about two percent of said first power level, wherein the first magnetic field and the correction magnetic field combine to yield the operational magnetic field during use; and

adjusting the operational magnetic field to a target magnetic field strength via monitoring the operational magnetic field to determine said second power level, wherein as a result of lower power consumption said second power level allows for more accurate and/or precise control of the operational magnetic field.

12. The method of claim 11, further comprising the step of:

monitoring the operational magnetic field with said magnetic field sensor, said magnetic field sensor yielding a magnetic field reading;

in a feedback loop, adjusting said second power using said magnetic field reading to obtain the target magnetic field strength.

13. The method of claim 11, further comprising the step of:

continuously adjusting the target magnetic field strength during x-axis and y-axis scanning of the charged particles in targeting the tumor.

14. The method of claim 11, further comprising the step of:

correcting magnetic field strength of at least two of said turning magnets with a single correction coil of said at least one correction coil.

15. The method of claim 11, further comprising the steps of:

accelerating the charged particles to an energy using said synchrotron;

focusing the charged particles with a focal system to a volume of less than about two millimeters in diameter; and

actively scanning the charged particles at the tumor with an active scanning system, wherein said active scanning system simultaneously scans the charged particles along all of;

a horizontal axis;

a vertical axis; and

a kinetic energy axis.

16. The method of claim 15, further comprising the step of:

concentrating the magnetic field with geometry of a core of at least one of said turning magnets, wherein a gap surface cross-section distance of said core comprises a first distance, wherein a core body cross-section distance of said core running parallel to said gap surface cross-section distance comprises a second distance at least one and a half times said surface cross-section distance.

17. The method of claim 11, further comprising the step of:

concentrating the magnetic field with geometry of a core of at least one of said turning magnets, wherein a correction coil wraps around said at least one of said turning magnets, said gap running through said core, wherein said geometry of said core expands from a magnetic field entrance dimension of said gap with an angle of about twenty to sixty degrees to a second core cross-section distance at least one and a half times larger than said magnetic field entrance dimension of said gap.

18. A method for irradiation of a tumor of a patient with charged particles, comprising the steps of:

accelerating the charged particle beam with a synchrotron;

focusing the charged particles with a focal system to a volume of less than about two millimeters in diameter;

controlling kinetic energy of the charged particles using at least one correction coil in said synchrotron; and

actively scanning the charged particles at the tumor with an active scanning system, wherein said active scanning system simultaneously scans the charged particles along all of;

a horizontal axis;

a vertical axis; and

a kinetic energy axis.

19. The method of claim 18, further comprising the step of:

rotating the patient to at least ten distinct irradiation positions and repeating said steps of accelerating, focusing, controlling, and scanning for each of said irradiation positions.