Charged particle cancer therapy X-ray method and apparatus
View Patent ↗The invention comprises an X-ray method and apparatus used in conjunction with charged particle or proton beam radiation therapy of cancerous tumors. The system uses an X-ray beam that lies in substantially the same path as a proton beam path of a particle beam cancer therapy system. The system creates an electron beam that strikes an X-ray generation source where the X-ray generation source is located proximate to the proton beam path. By generating the X-rays near the proton beam path, an X-ray path that is essentially the proton beam path is created. Using the generated X-rays, the system collects X-ray images of a localized body tissue region about a cancerous tumor. The generated image is usable for: fine tuning body alignment relative to the proton beam path, to control the proton beam path to accurately and precisely target the tumor, and/or in system verification and validation.
1. An X-ray apparatus as part of a particle beam cancer therapy system, said particle beam cancer therapy system irradiating a tumor of a patient with a charged particle beam during use, said apparatus comprising:
an X-ray generation source located within forty millimeters of the charged particle beam, wherein said X-ray source maintains a single static position: (1) during use of said X-ray source and (2) during tumor treatment with the charged particle beam; and
a synchrotron accelerating the charged particle beam, wherein said synchrotron comprises exactly four, ninety degree, turning sections,
wherein the tumor is targeted using X-ray images collected using X-rays from said X-ray generation source,
wherein the tumor is treated using the charged particle beam, and
wherein X-rays emitted from said X-ray source run substantially in parallel with the charged particle beam.
2. The apparatus of claim 1 , wherein said X-ray generation source comprises a tungsten anode.
3. The apparatus of claim 2 , further comprising:
an electron generating cathode;
a control electrode;
a plurality of accelerating electrodes;
a magnetic lens; and
a quadrupole magnet, all of said control electrode, said accelerating electrodes, said magnetic lens, and said quadrupole magnet located between said cathode and an X-ray generating anode in said X-ray generation source, said control electrode, said accelerating electrodes, said magnetic lens, and said quadrupole magnet combining to form a substantially parallel electron beam with an electron beam cross-sectional area, wherein a cross-sectional area of said cathode is greater than about eight times that of the electron beam cross-sectional area.
4. The apparatus of claim 3 , wherein said substantially parallel electron beam comprises an oblong cross-sectional shape, wherein geometry of said X-ray generation source yields an X-ray beam comprising a nearly circular cross sectional shape when struck by the electron beam having said oblong cross-sectional shape, the X-ray beam running substantially in parallel with the charged particle beam.
5. The apparatus of claim 4 , further comprising a cooling element connected to a backside of said tungsten anode.
6. The apparatus of claim 1 , wherein use of said X-ray generation source occurs within thirty seconds of subsequent use of the charged particle beam for tumor therapy.
7. The apparatus of claim 1 , wherein said synchrotron comprises:
exactly four turning sections; and
no quadrupoles in the circulating path of the synchrotron.
8. An X-ray method as part of a particle beam cancer therapy system, said particle beam cancer therapy system irradiating a tumor of a patient with a charged particle beam during use, said method comprising the steps of:
generating X-rays with an X-ray generation source located within forty millimeters of the charged particle beam, wherein said X-ray source maintains a single static position: (1) during use of said X-ray source and (2) during tumor treatment with the charged particle beam;
accelerating the charged particle beam with a synchrotron, wherein said synchrotron comprises:
exactly four turning sections; and
no quadrupoles in the circulating path of the synchrotron;
targeting the tumor targeted using X-ray images collected using X-rays from said X-ray generation source; and
treating the tumor using the charged particle beam,
wherein the X-rays emitted from said X-ray source run substantially in parallel with the charged particle beam.
9. The method of claim 8 , wherein said X-ray generation source comprises a tungsten anode.
10. The method of claim 9 , further comprising the step of:
generating electrons with a cathode, said cathode having a first cross-sectional distance, wherein the X-rays are generated by the electrons from said cathode striking said tungsten anode.
11. The method of claim 10 , further comprising the steps of:
focusing the electrons from said first cross-sectional distance to a second cross-sectional distance with a focusing control electrode; and
accelerating the electrons with accelerating electrodes, said focusing control electrode and said accelerating electrodes located between said cathode and said anode.
12. The method of claim 10 , further comprising the step of:
forming a substantially parallel electron beam with a control electrode, accelerating electrodes, a magnetic lens, and a quadrupole magnet, all of said control electrode, said accelerating electrodes, said magnetic lens, and said quadrupole magnet located between said cathode and said anode,
wherein the electron beam comprises a cross-sectional area, wherein a cross-sectional area of said cathode is greater than about eight times that of the electron beam cross-sectional area.
13. The method of claim 12 , further comprising the step of:
forming a substantially circular cross-section X-ray beam, wherein said substantially parallel electron beam comprises an oblong cross-sectional shape, wherein geometry of said X-ray generation source yields the substantially circular cross section X-ray when struck by the electron beam having said oblong cross-sectional shape, the X-ray beam running substantially in parallel with the charged particle beam.
14. The method of claim 12 , further comprising the step of:
cooling said tungsten anode with a cooling element connected to a backside of said tungsten anode.
15. The method of claim 8 , further comprising the step of:
using said X-ray generation source within thirty seconds of subsequent use of the charged particle beam for tumor therapy.
16. The method of claim 8 , wherein said synchrotron comprises:
exactly four, ninety degree, turning sections.