Proton dose monitoring with PET: quantitative studies in Lucite

Oelfke, Uwe; Lam, Gabriel K. Y.; Atkins, M. Stella

doi:10.1088/0031-9155/41/1/013

Cited by 135 publications

(110 citation statements)

References 11 publications

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“…The distribution of actual e + annihilation points is shown by the dashed histogram, while the distribution which accounts for a finite spatial PET resolution of FWHM = 8 mm is shown by the solid histogram. Points show experimental data (Oelfke et al 1996). correct for this difference, the experimental data in figure 3 were shifted by 3 -6 mm to ensure the same position of the Bragg peak in PMMA as reported by .…”

Section: Distribution Of Positron Annihilation Points As Measured By mentioning

confidence: 99%

Distributions of positron-emitting nuclei in proton and carbon-ion therapy studied with GEANT4

2006

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Abstract.Depth distributions of positron-emitting nuclei in PMMA phantoms are calculated within a Monte Carlo model for Heavy-Ion Therapy (MCHIT) based on the GEANT4 toolkit (version 8.0). The calculated total production rates of 11 C, 10 C and 15 O nuclei are compared with experimental data and with corresponding results of the FLUKA and POSGEN codes. The distributions of e + annihilation points are obtained by simulating radioactive decay of unstable nuclei and transporting positrons in surrounding medium. A finite spatial resolution of the Positron Emission Tomography (PET) is taken into account in a simplified way. Depth distributions of β + -activity as seen by a PET scanner are calculated and compared to available data for PMMA phantoms. The calculated β + -activity profiles are in good agreement with PET data for proton and 12 C beams at energies suitable for particle therapy. The MCHIT capability to predict the β + -activity and dose distributions in tissue-like materials of different chemical composition is demonstrated.

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Section: Distribution Of Positron Annihilation Points As Measured By mentioning

confidence: 99%

Distributions of positron-emitting nuclei in proton and carbon-ion therapy studied with GEANT4

2006

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“…The dose range is reported as a black dashed line in each plot. Dose range has been calculated given the depth of the Bragg peak in homogeneous PMMA, i.e., 29 mm (Oelfke et al 1996), starting from the activity rising edge. In figure 7 it can be seen how the image background noise is higher when the reconstruction is performed with low statistics, i.e., low dose (a)-(d), rather than with high dose rates (e)-(h).…”

Section: Distal Fall-off During and After The Irradiationmentioning

confidence: 99%

First full-beam PET acquisitions in proton therapy with a modular dual-head dedicated system

et al. 2013

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During particle therapy irradiation, positron emitters with half-lives ranging from 2 to 20 min are generated from nuclear processes. The half-lives are such that it is possible either to detect the positron signal in the treatment room using an in-beam positron emission tomography (PET) system, right after the irradiation, or to quickly transfer the patient to a close PET/CT scanner. Since the activity distribution is spatially correlated with the dose, it is possible to use PET imaging as an indirect method to assure the quality of the dose delivery. In this work, we present a new dedicated PET system able to operate in-beam. The PET apparatus consists in two 10 cm × 10 cm detector heads. Each detector is composed of four scintillating matrices of 23 × 23 LYSO crystals. The Content from this work may be used under the terms of the Creative Commons Attribution 3.0 licence.

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“…with energy E will be absorbed and undergo a nuclear reaction before the end of its range, the proton flux Φ(z) decreases as the depth z increases [9]:…”

Section: Proton Flux and Target Density Calculationsmentioning

confidence: 99%

Dependence of the Production Yields of Positron Emitters in Proton Therapy on the Cross Section Data Variations

Beebe‐Wang¹,

Peggs²,

Smith³

2003

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Earlier works, including a recent one at BNL, demonstrated that positron emission tomography (PET) is a potentially powerful tool for quality assurance and the treatment planning of Proton Therapy (PT). In particular, the PET images show the adequacy of the overlapping of the dose distribution with the intended target volume. Here, we present calculations of the possible variations in yields of positron emitters produced by proton beams of 250 MeV in a soft tissue, and combine the results with the Monte Carlo simulations of PET data collection from our recent work to show the effect of input data variations on the images. We demonstrate that the image results depend strongly on the available nuclear reaction cross section data.. The emphasis of this work is on determining, quantitatively, the differences in the calculated PET image yields resulting from four different sets of input nuclear reaction cross section data.

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Proton dose monitoring with PET: quantitative studies in Lucite

Cited by 135 publications

References 11 publications

Distributions of positron-emitting nuclei in proton and carbon-ion therapy studied with GEANT4

Distributions of positron-emitting nuclei in proton and carbon-ion therapy studied with GEANT4

First full-beam PET acquisitions in proton therapy with a modular dual-head dedicated system

Dependence of the Production Yields of Positron Emitters in Proton Therapy on the Cross Section Data Variations

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