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Fractionated stereotactic radiotherapy: A method to evaluate geometric and dosimetric uncertainties using radiochromic films
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10.1118/1.3134246
/content/aapm/journal/medphys/36/7/10.1118/1.3134246
http://aip.metastore.ingenta.com/content/aapm/journal/medphys/36/7/10.1118/1.3134246

Figures

Image of FIG. 1.
FIG. 1.

The TaPo is fixed on the stereotactic frame during the treatments. The five paper sheets placed on it show the projection of the isocenter and the micro-MLC shape at the beginning and at the end of each arc. In the example considered in the figure a double isocenter treatment is shown. The laser is positioned on the first isocenter.

Image of FIG. 2.
FIG. 2.

The couch mount is rigidly fixed to the couch and, using the four screws shown in the figure, it is possible to slightly adjust the TaPo position and tilt without moving the couch.

Image of FIG. 3.
FIG. 3.

Before each arc, after setting the right couch and collimator angles, we check if, with gantry angle set to 0°, the crosshair shadow coincides with the isocenter projection and, if not, we use the lateral and the longitudinal fine adjustment screws placed in the couch mount to correct such a misalignment. (a) After that, we set the right start and stop gantry angles and check if the field light coincides with the shape printed on the TaPo. (b) If not, we adjust the vertical screw, or, if it is not enough, a combination of the other screws (tilt, lateral, and longitudinal). When everything is okay, we treat the patient.

Image of FIG. 4.
FIG. 4.

Treatment plans for the three sets of measurements. (a) The first plan refers to sets 1 and 2, (b) while the second one refers to set 3. In both plans the arc positions are the same (couch at 330°, 300°, 90°, 60°, and 30°), while arc extensions are different in order to be suited to the two different geometric conditions. The micro-MLC leaves are optimized in order to cover the PTV periphery with the 80% isodose. (a) For sets 1 and 2 the PTV is spherical and placed in the middle of the skull, (b) while for set 3 the PTV is irregular and placed in the skull periphery.

Image of FIG. 5.
FIG. 5.

“Grey level–dose” calibration for Gafchromic EBT films. The red channel (○) shows the highest sensitivity, especially up to 500 cGy.

Image of FIG. 6.
FIG. 6.

A Gafchromic EBT film (a) before and (b) after registration with the corresponding (c) calculated dose matrix. Such film refers to the third set of measurements (irregular PTV, far from the middle).

Image of FIG. 7.
FIG. 7.

(a) A pierced Gafchromic film fixed onto a phantom slice. In the upper right corner a magnified hole is shown. (b) The same film is entirely encompassed by a single CT scan. The five holes in the phantom slice, through which the film is pierced, are clearly visible.

Image of FIG. 8.
FIG. 8.

Schematic representation of the relationship among FLE, FRE, and TRE. (a) A dose matrix with two target points (1 and 2) and four fiducials, indicated by small circles and supposed to be without localization error for simplicity, is shown. The reference system has its origin in the fiducial centroid. (b) A digitized film with the four fiducials, indicated by crosses and characterized by a localization error (schematized as arrows from the “correct” localizations) is shown. The reference system has its origin in the new fiducial centroid and is oriented differently from . In order to simplify any comparison with the dose matrix, the four correctly localized fiducials, the reference system, and the two target points are displayed. (c) The digitized film has been shifted and rotated to minimize the root mean square distance between homologous fiducials (linked by double tip arrows) that is coregistrated with the dose matrix. The root mean square residual error after coregistration is the FRE and its value is returned by the FILMQA software. The TRE is the localization error in special points of interest: If the point is close to the fiducial centroid (target 1), the overall error is quite small and mainly due to the translational component, while if the point is far from the centroid (target 2), the rotational component becomes large and makes the overall error larger.

Image of FIG. 9.
FIG. 9.

Measurement technique of isocenter displacements. (a) A dose matrix image with four fiducials and the 80% isodose and (b) a digitized film with the corresponding four fiducials (supposed to be without localization error for simplicity) and the 80% isodose are shown. (c) After the image coregistration the homologous fiducials coincide, while the 80% isodose curves are slightly shifted because of geometric uncertainties. (d) and , the shifts necessary to make the two isodose curves coincident or concentric, are the quantities that we consider as repositioning errors.

Image of FIG. 10.
FIG. 10.

80% computed (thick line) and measured (thin line) isodose curves (a) after registration with the corresponding dose matrix and (b) after shifting the film by 0.9 mm in the direction and by 1.1 mm in the direction. Such movements are necessary to make the curves concentric and represent the isocenter positioning error.

Image of FIG. 11.
FIG. 11.

Measurements of isocenter repositioning errors. (×) Set 1: spherical PTV in the middle, no TaPo. (○) Set 2: spherical PTV in the middle, TaPo mounted. (△) Set 3: irregular PTV in the periphery, TaPo mounted. The arrows represent the systematic errors, while the ellipse and semiaxes represent the standard deviations, that is, the random errors, in the same directions. The use of TaPo decreases both systematic and random errors, while the peripheral position of the PTV increases just the systematic error, leaving the random error unchanged.

Tables

Generic image for table
TABLE I.

Characteristics of the three sets of measurements: PTV shape, PTV position in the skull, and use of TaPo.

Generic image for table
TABLE II.

Translational and rotational components of the TRE and ratio TRE/FLE in the two different experimental conditions. In the first two measurement sets is negligible with respect to , while in the third set, characterized by a geometrical asymmetry, becomes comparable to . Their sum does not change much because of the increment of the fiducial number from 5 to 9 and so the TRE remains about 45% of the FLE in both configurations.

Generic image for table
TABLE III.

Registration errors (FRE, FLE, and TRE) in the three measurement sets. As TREs are always less than 0.05 mm, that is, much smaller than the quantities we want to measure, we are sure that the registration procedure does not affect the results of our measurements.

Generic image for table
TABLE IV.

Average percentage shifts from expected dose value (5 Gy) and standard deviations of the five measurements in the three experimental conditions.

Generic image for table
TABLE V.

(LL), (AP), and radial isocenter displacements in the three measurement sets. Each quantity is expressed as mean value and standard deviation of the five measurements.

Generic image for table
TABLE VI.

Differences between measured and computed radial extensions of reference isodose ( of 500 cGy). If we consider that the isocenter dose value can be slightly different from the nominal one and measure the same quantities referring to the 80% of the measured isocenter dose value, we obtain much closer values. Each quantity is expressed as mean value and standard deviation of the five measurements.

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/content/aapm/journal/medphys/36/7/10.1118/1.3134246
2009-06-09
2014-04-20
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752b84549af89a08dbdd7fdb8b9568b5 journal.articlezxybnytfddd
Scitation: Fractionated stereotactic radiotherapy: A method to evaluate geometric and dosimetric uncertainties using radiochromic films
http://aip.metastore.ingenta.com/content/aapm/journal/medphys/36/7/10.1118/1.3134246
10.1118/1.3134246
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