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Fast patient-specific Monte Carlo brachytherapy dose calculations via the correlated sampling variance reduction technique
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10.1118/1.3679018
/content/aapm/journal/medphys/39/2/10.1118/1.3679018
http://aip.metastore.ingenta.com/content/aapm/journal/medphys/39/2/10.1118/1.3679018

Figures

Image of FIG. 1.
FIG. 1.

Plots of distributions, dots, for prostate (a) and breast (b) with their corresponding fits, line. Fit parameters are in Table II.

Image of FIG. 2.
FIG. 2.

Scatter plot of the efficiency gain vs the HCF for all voxels in the prostate (a) and breast (b) geometries; scatter plot of the efficiency gain vs the delivered dose (Gy) for all voxels in the prostate (c) and breast (d) geometries. The area outlined in circumscribes the voxels originating from the CTV.

Image of FIG. 3.
FIG. 3.

Scatter plot of percent standard deviation about the mean vs dose for each individual voxel within the prostate (a), urethra (b), and the rectum (c), for correlated Monte Carlo (lower) and uncorrelated Monte Carlo (upper). The average percent standard deviation about the mean value for correlated Monte Carlo is plotted as green line. The CPU time was 39 s.

Image of FIG. 4.
FIG. 4.

Scatter plot of percent standard deviation about the mean vs dose for each individual voxel within the breast CTV (a), and the breast simulated lumpectomy cavity (b) for correlated Monte Carlo (lower) and uncorrelated Monte Carlo (upper). The average percent standard deviation about the mean value for correlated Monte Carlo is plotted as green line. The CPU time is 21 s.

Image of FIG. 5.
FIG. 5.

Isodose curves for low-uncertainty uncorrelated Monte Carlo (dashed lines) and correlated Monte Carlo (solid) for prostate (a) and breast (b) using CPU times. All calculations use the finest dose grid.

Image of FIG. 6.
FIG. 6.

Scatter plot of G ijk vs HCF for all voxels in the simulated breast plan for correlated Monte Carlo based upon generation of photon histories in homogeneous water rather than average breast medium. The area outlined in red circumscribes the voxels originating from the CTV.

Tables

Generic image for table
TABLE I.

Symbols listed in order of appearance.

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TABLE II.

Best fit parameters values of the distribution, Eq. (8), for the breast and prostate plans.

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TABLE III.

Average efficiency gain for the breast and prostate plans for various ROI’s along with the estimated time required to compute Monte Carlo dose to achieve 2% mean standard deviations about the mean. For the prostate plan, data are given for three different voxel dimensions: (1.0 mm)3, (2.0 mm)3, and (3.0 mm)3 relative to uncorrelated Monte Carlo. Percentages within parentheses are the percentage of voxels within the corresponding structure that experience and efficiency gain greater than unity. The times listed are estimated to achieve average 2% standard deviation about the mean within corresponding structure at all dose levels.

Generic image for table
TABLE IV.

G20,G50, and G90 (average efficiency gain for voxels receiving greater than or equal to 20%, 50%, and 90% of the prescribed dose, respectively) for the breast and prostate plans. The prostate also shows values for larger voxel dimensions (2mm and 3mm). The percentage of the voxel contained in these regions that experience and efficiency gain are contained within the parentheses.

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/content/aapm/journal/medphys/39/2/10.1118/1.3679018
2012-02-03
2014-04-16
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752b84549af89a08dbdd7fdb8b9568b5 journal.articlezxybnytfddd
Scitation: Fast patient-specific Monte Carlo brachytherapy dose calculations via the correlated sampling variance reduction technique
http://aip.metastore.ingenta.com/content/aapm/journal/medphys/39/2/10.1118/1.3679018
10.1118/1.3679018
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