Abstract

There are drawbacks with using a Positron Emission Tomography (PET) scanner design employing the traditional arrangement of multiple detectors in an array format. Typically PET systems are constructed with many regular gaps between the detector modules in a ring or box configuration, with additional axial gaps between the rings. Although this has been significantly reduced with the use of the compact high granularity SiPM photodetector technology, such a scanner design leads to a decrease in the number of annihilation photons that are detected causing lower scanner sensitivity. Moreover, the ability to precisely determine the line of response (LOR) along which the positron annihilated is diminished closer to the detector edges because the spatial resolution there is degraded due to edge effects. This happens for both monolithic based designs, caused by the truncation of the scintillation light distribution, but also for detector blocks that use crystal arrays with a number of elements that are larger than the number of photosensors and, therefore, make use of the light sharing principle. In this report we present a design for a small-animal PET scanner based on a single monolithic annulus-like scintillator that can be used as a PET insert in high-field Magnetic Resonance systems. We provide real data showing the performance improvement when edge-less modules are used. We also describe the specific proposed design for a rodent scanner that employs facetted outside faces in a single LYSO tube. In a further step, in order to support and prove the proposed edgeless geometry, simulations of that scanner have been performed and lately reconstructed showing the advantages of the design.

Highlights

  • Preclinical imaging instrumentation has substantially improved over the past decade [1]

  • Positron Emission Tomography (PET) instrumentation typically relies on multiple detector modules optimized for 511 keV annihilation photons detection arranged in an annular or multipanel geometry

  • Most PET scanners make use of scintillators based on a pixelated design in which the raw scintillator crystal is cut into small elements to produce arrays of optically isolated pixels in order to spatially localize the scintillation event in the crystal block

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Summary

Introduction

Preclinical imaging instrumentation has substantially improved over the past decade [1]. Other geometries have been described in the literature [3,4,5,6,7,8,9] These modules in most cases are built on the basis of a scintillation crystal block and a photosensor array. Most PET scanners make use of scintillators based on a pixelated design in which the raw scintillator crystal is cut into small elements (pixels) to produce arrays of optically isolated pixels in order to spatially localize the scintillation event in the crystal block. DOI is achieved using multiple layers of crystal pixel arrays either staggered or made of different scintillator material [phoswich type [10,11,12,13]]. More involved and complicated designs make use of double-sided readout with additional photo-sensors at the gamma entry faces to accurately deduce the DOI [14]

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