Dosimetric scintillating screen detector for charged particle radiotherapy quality assurance (QA)

• US 9,958,402 B2
• Filed: 02/25/2013
• Issued: 05/01/2018
• Est. Priority Date: 02/23/2012
• Status: Active Grant

• Current Assignee: Steven M. Ebstein
• Original Assignee: Steven M. Ebstein
• Inventors: Ebstein, Steven M.
• Primary Examiner(s): Porta, David
• Assistant Examiner(s): Faye, Mamadou
• Application Number:
  US13/775,325
• Publication Number:
  US 20130287170A1
• Time in Patent Office: 1,891 Days
• Field of Search: 2503361
• CPC Class Codes: A61N 2005/1076 using a dummy object placed in the radiation field, e.g. phantom
• CPC Class Codes: A61N 5/1075 for testing, calibrating, or quality assurance of the radiation treatment apparatus
• CPC Class Codes: G01N 23/04 and forming images of the material

Abstract

An apparatus and method are provided for performing Quality Assurance of complex beams of penetrating radiation inside a patient. A detector with a transverse scintillating screen images the radiation inside a tissue phantom with high spatial resolution. The scintillator is comprised of a mixture of two or more scintillators emitting different spectra of light and having different characteristic responses as a function of the beam LET value. The optics relaying the scintillation output have variable transmission with wavelength, further shaping the spectrum of light transmitted to the imaging sensor which also has spectrally varying sensitivity. Parameters of the scintillator construction, the optics, and the imaging sensor are chosen so the output of the composite detector is proportional to a characteristic of the input beam, for example the dose deposited as a function of depth inside the tissue phantom.

Claims

1. A method for determining the spatial distribution and intensity of a penetrating radiation beam characterized generally by a propagation direction inside a body, the method comprising:

providing a tissue phantom between a radiation source and a radiation detector;

providing a scintillating screen disposed behind the tissue phantom for emitting light in response to the radiation received by the scintillating screen, the scintillating screen comprising a mixture of at least two scintillators wherein each scintillator has a different characteristic response and a different spectral output;

providing a means of optical communication between the output of the scintillating screen and at least one imaging sensor, wherein the means of optical communication has a nonuniform spectral transmission; and

providing the at least one imaging sensor in optical communication with the scintillating screen for providing a high resolution imaging sensor output indicative of the spatial distribution and intensity of the radiation beam, wherein the imaging sensor has a nonuniform spectral sensitivity;

wherein the composition of the scintillating screen, the means of optical communication, and the at least one imaging sensor are selected, based on their spectral properties, so as to form a first system wherein the relative contributions of the at least two scintillators of the mixture produce an imaging sensor output which is proportional to a characteristic of the radiation beam incident on the scintillating screen at each measurement position accessible with the tissue phantom; and

performing characteristic measurements with a penetrating radiation beam and the first system;

adjusting the means of optical communication wherein the adjusted means of optical communication has a different spectral transmission than the original;

wherein the adjusted means of optical communication is selected, based on its spectral properties, so as to form a second system wherein the relative contributions of the at least two scintillators of the mixture produce an imaging sensor output which is proportional to a characteristic of the radiation beam incident on the scintillating screen at each measurement position accessible with the tissue phantom with greater accuracy than with the first system; and

exposing the second system to a beam of penetrating radiation to produce the high resolution imaging sensor output.

2. The method as set forth in claim 1 wherein the adjustment comprises one of (a) the addition of an optical filter and (b) the replacement of an optical filter.

3. The method as set forth in claim 1 wherein the characteristic of the radiation beam includes the fluence.

4. The method as set forth in claim 1, wherein the characteristic of the radiation beam is the dose.

5. The method as set forth in claim 1, wherein the characteristic of the radiation beam is the response of an ion chamber.

6. The method as set forth in claim 1, wherein the characteristic of the radiation beam is the relative biological efficiency.

7. The method as set forth in claim 1, wherein the scintillating screen comprises a mixture of at least two inorganic scintillators.

8. The method as set forth in claim 1, wherein the at least two scintillators are chosen from the group consisting of P11, P20, P43, P46, and P47.

9. The method as set forth in claim 1, wherein the at least two scintillators comprise P11 and P43.

10. The method as set forth in claim 1, wherein the scintillating screen comprises a planar screen disposed perpendicular to the propagation direction of the radiation beam.

11. The method as set forth in claim 1, wherein the means of optical communication comprise a fold mirror and a compound lens.

12. The method as set forth in claim 1, wherein the at least one imaging sensor comprises a CCD.

13. The method as set forth in claim 1, wherein the tissue phantom comprises polymer sheets.

14. The method as set forth in claim 1 wherein the tissue phantom comprises water.

15. The method as set forth in claim 1 wherein the means of optical communication include at least one filter with nonuniform spectral transmission.

16. The method as set forth in claim 1 wherein the means of optical communication include at least one filter with variable nonuniform spectral transmission.

17. The method as set forth in claim 1 wherein the means of optical communication include a dichroic mirror which separates the light emitted by the scintillating screen into two substantially non-overlapping spectral bands and forms two spatially distinct images on the at least one imaging sensor, and further wherein the two spatially distinct images are linearly combined to produce the high resolution imaging sensor output.

18. The method as set forth in claim 1 wherein the at least one imaging sensor forms a multi-color image.