OC-0255: Correction function for MOSkin readings in realtime in vivo dosimetry in HDR prostate brachytherapy

Purpose or Objective: The development of MR-guided HDR brachytherapy has gained an increasing interest for delivering a high tumor dose safely.However, the update rate of MRbased needle localization is inherently low and the required image interpretation is hampered by signal voids arising from blood vessels or calcifications, which limits the precision of the needle steering.This study aims to assess the potential of fiber optic sensing for real-time needle tracking during MR-guided intervention.For this, the MR compatibility of a fiber optic tracking system and its accuracy are evaluated. Material and Methods: Fiber optic tracking device:The device consists of a flexible stylet with three optic fibers embedded along its length, a broadband light source, a spectrum analyzer and a PC with Labview application.Along each fiber, Bragg gratings are evenly spaced at 20 mm intervals.To reconstruct the shape of a needle, the stylet is inserted inside the lumen of the needle.This set-up placed in the 1.5T MR-scanner provides real-time measurement of the needle profile, without adverse imaging artefacts since no ferromagnetic material is involved.MRI-acquisition protocol: 3D MR-images were acquired with a 1.5T MR-scanner, using a 3D Spectral Presaturation with Inversion Recovery (SPIR) sequence (TR=2.9ms,TE=1.44ms, voxel size= 1.2×1.45×1mm^3,FOV=60×250×250mm^3). Experimental evaluation:The two following experiments were conducted:1.A needle was placed inside the MR-bore and its shape was imposed by a specially designed plastic mold with different known paths (see Fig. 1a).For path 1, 2 and 3, the shape of the needle was measured by fiber optic tracking during MR-imaging along 4 orientations (i.e 0°, 90°, 180°, 270°), by rotating the needle along its longitudinal axis.2. Four plastic catheters were introduced in an agar phantom.The corresponding catheter shapes were measured with fiber optic sensing during simultaneous MR imaging (see Fig. 1d, phantom shifted out of scanner for photograph).The MRbased needle shape stemmed from a segmentation step followed by a polynomial fitting (order 5).A rigid registration of the obtained MR-based needle model and the fiber optic tracking was then performed.Assessment of the fiber optic tracking: The fiber optic needle tracking accuracy was quantified by calculating the Euclidian distances between: the gold-standard shapes and fiber optic based measurements (Experiment #1); MR-and fiber optic based measurements (Experiment #2).Results: For all tested needle shapes, the maximum absolute difference between the fiber optic based and the goldstandard values was lower than 0.9mm (Experiment #1, Fig. 1b and 1c).Over the 4 tested catheters, the maximal absolute difference between MR-and fiber optic based measurements was lower than 0.9mm (Experiment #2, Fig. 1e, 1f and 1g).Conclusion: This study demonstrates that the employed fiber optic tracking device is able to monitor the needle bending during MR-imaging with an accuracy and update rate eligible for MR-guided intervention.

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