Method for pre treatment verification in radiation therapy

1. A method of measuring dose distribution in a phantom for radiation therapy treatment verification, wherein at least two detector planes are arranged in said phantom in a non-parallel manner, each plane being provided with a plurality of diode detectors, wherein said phantom is irradiated using a patient specific treatment, comprising:

obtaining information regarding the dose distribution inside said phantom by performing measurements using said detectors;

dividing the measurements in time-intervals, each time-interval having maximum length of approximately 100 msec; and

using said information in the treatment verification.

2. A method according to claim 1 , wherein the information obtained by said measurements is used for IMRT verification.

3. A method according to claim 1 , wherein said irradiation of the phantom comprises delivering dose pulses, the method further comprising synchronizing the measurements with said delivered doses.

4. A method according to claim 1 , further comprising: synchronizing the measurements with a respiratory cycle of the patient for which the patient specific treatment is intended; and determining the dose delivered in the various phases of the respiratory cycle.

5. A method according to claim 1 , further comprising the step of storing the data for each specific time-interval for measurements in said phantom.

6. A method according to claim 1 , further comprising the step of calculating a correction factor for each detector element for each time-interval using said obtained information regarding the dose distribution inside said phantom.

7. A method according to claim 6 , wherein each correction factor Corr n, f, seg−n, f, p, t(i), t(i+1) is calculated according to:

Corr n, f, seg−n, f, p, t(i), t(i+1) =C dir *C depth *C pos ,

where:

Corr n, f, seg−n, f, p, t(i), t(i+1) is the correction factor to be used with detector element n, in the sub field f in the phantom, correcting the measured dose integrated from time t(i) until t(i+1) to achieve the dose in the point of location of detector n,

C dir is a factor correcting for any directional dependence in detector n,

C depth is a factor correcting for any depth, energy and/or dose rate, in detector n, and

C pos is a factor correcting for position dependency in detector n.

8. A method according to claim 6 , wherein each correction factor Corr n, f, seg−n, f, p, t(i), t(i+1) is calculated according to:

Corr n, f, seg−n, f, p, t(i), t(i+1) =C dir +C depth +C pos ,

where:

Corr n, f, seg−n, f, p, t(i), t(i+1) is the correction factor to be used with detector element n, in the sub field f in the phantom, correcting the measured dose integrated from time t(i) until t(i+1) to achieve the dose in the point of location of detector n,

C dir is a factor correcting for any directional dependence in detector n,

C depth is a factor correcting for any depth, energy and/or dose rate, in detector n, and

C pos is a factor correcting for position dependency in detector n.

9. A method according to claim 1 , wherein the detector planes are arranged such that for each angle projection of a radiation beam used to irradiate said phantom, either of said non-parallel planes intersects with all parts of the radiation beam.

10. A method according to claim 1 , wherein each detector plane is provided with detectors having a thickness in a range less than a range of electrons in a radiation beam used to irradiate said phantom where energy dependency is significant.

11. A detector configuration for use in the method according to claim 1 , where the detector configuration is arranged in a phantom suitable for radiation therapy and comprises at least two detector planes provided with a plurality of diode detectors for measuring irradiation in said phantom, said irradiation being delivered using a patient specific treatment, wherein said planes being arranged in a non-parallel manner, wherein each of said detector planes has a thickness less than 500 μm.

12. Detector configuration according to claim 11 , wherein each of said detector planes has a thickness of less than 200 μm.

13. Diode detector according to claim 1 , wherein said detector is used in water phantom dosimetry or in vivo dosimetry during Brachy therapy in Radio therapy.

14. A computer-readable medium embodied in a tangible medium comprising instructions which when implemented by a computer, cause the computer to perform the steps of the method according to claim 1 .

15. A method of measuring dose distribution in a phantom for radiation therapy treatment verification, wherein detector planes are arranged in said phantom, each plane being provided with a plurality of diode detectors, wherein said phantom is irradiated using a patient specific treatment, comprising:

obtaining information regarding the dose distribution inside said phantom by performing measurements using said detectors;

dividing the measurements in time-intervals, each time-interval having a maximum length of approximately 100 msec;

synchronizing the measurements with a respiratory cycle of a patient for which the patient specific treatment is intended;

determining the dose delivered in the various phases of the respiratory cycle; and

using said information in the treatment verification.

16. A method according to claim 15 , wherein at least two detector planes are arranged in said phantom in a non-parallel manner.

17. An apparatus for measuring dose distribution in a phantom for radiation therapy treatment verification where said phantom is irradiated using a patient specific treatment, comprising:

at least two detector planes arranged in said phantom in a non-parallel manner, each plane being provided with a plurality of diode detectors, and

electronic circuitry configured to:

obtain information regarding the dose distribution inside said phantom by performing measurements using said detectors;

divide the measurements in time-intervals, each time-interval having maximum length of approximately 100 msec; and

use said information in the treatment verification.

18. The apparatus in claim 17 , wherein irradiation of the phantom comprises delivered dose pulses, and wherein the electronic circuitry is configured to synchronize the measurements with said delivered doses.

19. The apparatus in claim 17 , wherein the electronic circuitry is configured to:

synchronize the measurements with a respiratory cycle of the patient for which the patent specific treatment is intended, and

determine the dose delivered in the various phases of the respiratory cycle.

20. The apparatus in claim 17 , wherein the electronic circuitry is configured to calculate a correction factor for each detector element for each time-interval using said obtained information regarding the dose distribution inside said phantom.

21. The apparatus in claim 20 , wherein the electronic circuitry is configured to calculate each correction factor Corr n, f, seg−n, f, p, t(i), t(i+1) according to:

Corr n, f, seg−n, f, p, t(i), t(i+1) =C dir *C depth *C pos , where:

Corr n, f, seg−n, f, p, t(i), t(i+1) is the correction factor to be used with detector element n, in the sub field f in the phantom, correcting the measured dose integrated from time t(i) until t(i+1) to achieve the dose in the point of location of detector n,

C dir is a factor correcting for any directional dependence in detector n,

C depth is a factor correcting for any depth, energy and/or dose rate, in detector n, and

C pos is a factor correcting for position dependency in detector n.

22. The apparatus in claim 20 , wherein the electronic circuitry is configured to calculate each correction factor Corr n, f, seg−n, f, p, t(i), t(i+1) is calculated according to:

Corr n, f, seg−n, f, p, t(i), t(i+1) =C dir +C depth +C pos , where:

Corr n, f, seg−n, f, p, t(i), t(i+1) is the correction factor to be used with detector element n, in the sub field f in the phantom, correcting the measured dose integrated from time t(i) until t(i+1) to achieve the dose in the point of location of detector n,

C dir is a factor correcting for any directional dependence in detector n,

C depth is a factor correcting for any depth, energy and/or dose rate, in detector n, and

C pos is a factor correcting for position dependency in detector n.

23. The apparatus in claim 17 , wherein the detector planes are arranged such that for each angle projection of a radiation beam used to irradiate said phantom, either of said non-parallel planes intersects with all parts of the radiation beam.

24. An apparatus for measuring dose distribution in a phantom for radiation therapy treatment verification, wherein detector planes are arranged in said phantom, each plane being provided with a plurality of diode detectors, wherein said phantom is irradiated using a patient specific treatment, comprising:

means for obtaining information regarding the dose distribution inside said phantom by performing measurements using said detectors;

means for dividing the measurements in time-intervals, each time-interval having a maximum length of approximately 100 msec;

means for synchronizing the measurements with a respiratory cycle of a patient for which the patient specific treatment is intended;

means for determining the dose delivered in the various phases of the respiratory cycle; and

means for using said information in the treatment verification.