Monte Carlo simulation of a proton therapy beamline for intracranial treatments

Sayah, R.; Donadille, L.; Aubé, A.; Hérault, J.; Delacroix, S.; Marzi, Ludovic De; Stichelbaut, F.; Clairand, I.

doi:10.1051/radiopro/2012054

Cited by 11 publications

(22 citation statements)

References 20 publications

(37 reference statements)

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“…The study by Sayah et al (2013) focused on the modeling of the CPO's gantry room and beamline considering a 178 MeV proton beam to treat a 5.5-cm-diameter spherical craniopharyngioma. This imposed the selection of one specific set of FS, RMW and SS (cf.…”

Section: Beamline Configurations and Validation Setupmentioning

confidence: 99%

“…Table 1). The geometry and composition of these elements and the treatment room were carefully reproduced and calculations were carried out and benchmarked against experimental measurements both for protons (Sayah et al, 2013) and stray neutrons to validate the MC model.…”

Section: Beamline Configurations and Validation Setupmentioning

confidence: 99%

“…Next, a comprehensive validation is required to prove the reliability and accuracy of the MC model. Calculations are hence usually compared against experimental measurements of the proton dose, namely percentage depth dose (PDD) distributions and relative lateral dose profiles (Hérault et al, 2005;Newhauser et al, 2005;Polf et al, 2007;Sayah et al, 2013). The comparison should also be made for secondary neutron particles .…”

Section: Introductionmentioning

confidence: 99%

“…To carry out a comprehensive MC calculation of secondary neutron doses, the different dedicated beamline elements for the CPO's gantry beamline thus need to be modeled and validated. Previous work by Sayah et al (2013) was hence undertaken to model the CPO's gantry room and beamline in a single configuration representing one particular craniopharyngioma treatment. The current paper greatly extends the previous work by modeling all available sets of beamline elements while also covering the entire proton beam energy range regularly used at the CPO for intracranial tumor treatments, from ∼160 MeV to ∼220 MeV at the beamline entrance.…”

Section: Introductionmentioning

confidence: 99%

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Benchmarking Monte Carlo simulations against experimental data in clinically relevant passive scattering proton therapy beamline configurations

et al. 2016

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Monte Carlo simulations are widely used to calculate secondary neutron doses in proton therapy. When using the passive scattering technique, a small variation in the tumor size or location requires a full adjustment of the beamline configuration. This work thus focuses on modeling all possible beamline elements of the local facility with the MCNPX code while covering the entire clinical range of proton beam energies. This paper documents the experimental validation of realistic beamline configurations dedicated to intracranial tumor treatments, with different sources and beamline elements. Simulations were compared against measurements and treatment planning system (TPS) data considering percentage depth dose distributions (PDD) and relative lateral dose profiles. The results show that simulated and measured PDD distributions differ by no more than 1.6 mm on the proton beam range (tolerance set at 2 mm/2%) for the 162 MeV configuration. Meanwhile, for the modulated lateral dose profiles, the 219 MeV configuration presented the largest difference for the in-plane field width at 90% with 2 mm difference in measurements. The modeled proton sources and beamline elements were validated, and the new realistic geometries can be used to calculate secondary neutron doses to healthy tissues.

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Section: Beamline Configurations and Validation Setupmentioning

confidence: 99%

Section: Beamline Configurations and Validation Setupmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

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Benchmarking Monte Carlo simulations against experimental data in clinically relevant passive scattering proton therapy beamline configurations

et al. 2016

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“…These benefits derive from focusing high doses on the target volume while minimizing damage to surrounding normal tissue . Furthermore, application of out‐of‐field doses in active scanning beam (ASB) CIRT result not only in lower doses to organs at risk than passive beam (PB) CIRT but also dose reduction from secondary neutrons . Hence, beam delivery is shifting from PB CIRT to ASB CIRT in clinical practice.…”

Section: Introductionmentioning

confidence: 99%

Monte Carlo study of out‐of‐field exposure in carbon‐ion radiotherapy: Organ doses in pediatric brain tumor treatment

2019

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Purpose To estimate out‐of‐field doses during carbon‐ion radiotherapy (CIRT) for pediatric cerebellar ependymoma. Methods Given that the out‐of‐field dose of CIRT depends on beam parameters, we set them for treatment of typical pediatric cerebellar ependymoma based on a previous study. The out‐of‐field dose during CIRT for pediatric cerebellar ependymoma was then estimated using the Particle and Heavy‐Ion Transport code System with Monte Carlo simulations and a computational phantom developed at the University of Florida. From the simulation results, out‐of‐field doses at dose equivalents of passive beam and active scanning beam CIRT were calculated and compared to the secondary neutron‐equivalent dose of passive beam CIRT and proton therapy. Results The out‐of‐field dose equivalent decreases from 1.45 mSv/Gy (relative biological effectiveness — RBE) at the thyroid to 0.06 mSv/Gy (RBE) at the bladder, verifying decay as the distance from the treatment target increases. The out‐of‐field neutron‐equivalent dose in organs per prescribed dose for passive beam CIRT is lower than that for passive beam proton therapy. Moreover, the out‐of‐field organ dose equivalent per prescribed dose for the active scanning beam CIRT is lower than that for the passive beam CIRT. Conclusions Active scanning beam CIRT is promising for pediatric cerebellar ependymoma regarding out‐of‐field exposure, outperforming the comparison radiotherapy modalities.

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