Minimization of Parallax Error in Dedicated Breast PET

The increase of the detector thickness and the incidence angle of impinging photons permits an enhancement of sensitivity in positron emission tomography (PET) scanners. But also increases the parallax error and leads to a worsening of spatial resolution. Instead of introducing hardware modifications in the readout electronics or in the detector, we propose in this work to model the photon penetration depth in the detector material and to account for this effect during the image reconstruction. The validation of the model was based on experimental measurements with the MAMMI breast dedicated PET. It consists of twelve detector modules of monolithic LYSO scintillators. A point-like source was acquired at several radial positions across the field of view. The performance of the model was analyzed in terms of position accuracy and spatial resolution. Full width at half maximum (FWHM) average improvement values of 1.0 mm (radial), 0.4 mm (tangential), and 0.3 mm (axial) have been measured when the photon penetration depth was taken into account. The use of the model proposed in this work allows us to design PET detectors with improved sensitivity while maintaining the spatial resolution of the scanner.

[1]  J. G. Rogers,et al.  A practical block detector for a depth encoding PET camera , 1995 .

[2]  Yong Choi,et al.  Optimization of LSO/LuYAP phoswich detector for small animal PET , 2007 .

[3]  F. Sánchez,et al.  Design and evaluation of the MAMMI dedicated breast PET. , 2012, Medical physics.

[4]  Kisung Lee,et al.  Impact on Image Noise of Incorporating Detector Blurring Into Image Reconstruction for a Small Animal PET Scanner , 2009, IEEE Transactions on Nuclear Science.

[5]  A. Sebastia,et al.  Depth of /spl gamma/-ray interaction within continuous crystals from the width of its scintillation light-distribution , 2005, IEEE Transactions on Nuclear Science.

[6]  A. Sebastia,et al.  Scanner calibration of a small animal PET camera based on continuous LSO crystals and flat panel PSPMTs , 2007 .

[7]  R. Leahy,et al.  Accurate geometric and physical response modelling for statistical image reconstruction in high resolution PET , 1996, 1996 IEEE Nuclear Science Symposium. Conference Record.

[8]  Antonio Javier González Martínez,et al.  Design and First Results of an Innovative and Dedicated Breast PET , 2012 .

[9]  William W. Moses,et al.  Design studies for a PET detector module using a PIN photodiode to measure depth of interaction , 1994 .

[10]  Huafeng Liu,et al.  Development of a depth of interaction detector for γ-rays , 2001 .

[11]  Laura Moliner,et al.  Attenuation correction without transmission scan for the MAMMI breast PET , 2011 .

[12]  F Sanchez,et al.  Small animal PET scanner based on monolithic LYSO crystals: performance evaluation. , 2012, Medical physics.

[13]  R. Leahy,et al.  High-resolution 3D Bayesian image reconstruction using the microPET small-animal scanner. , 1998, Physics in medicine and biology.

[14]  F Sanchez,et al.  Design and evaluation of the MAMMI dedicated breast PET. , 2012, Medical physics.

[15]  C. Moisan,et al.  Segmented LSO crystals for depth-of-interaction encoding in PET , 1997, 1997 IEEE Nuclear Science Symposium Conference Record.

[16]  Thomas K. Lewellen,et al.  Modeling and incorporation of system response functions in 3-D whole body PET , 2006, IEEE Transactions on Medical Imaging.

[17]  Uwe Pietrzyk,et al.  Design optimization of the PMT-ClearPET prototypes based on simulation studies with GEANT3 , 2002 .

[18]  Yiping Shao,et al.  Simple charge division readouts for imaging scintillator arrays using a multi-channel PMT , 1995, 1995 IEEE Nuclear Science Symposium and Medical Imaging Conference Record.

[19]  L. Shepp,et al.  Maximum Likelihood Reconstruction for Emission Tomography , 1983, IEEE Transactions on Medical Imaging.