Abstract

In this study, we propose a staggered three-layer depth-of-interaction (DOI) detector with a 1 mm crystal pitch and 19.8 mm total crystal thickness for a high-resolution and high-sensitivity small animal in-beam PET scanner. A three-layered stacked LYSO scintillation array (0.9 × 0.9 × 6.6 mm3 crystals, 23 × 22 mm2 surface area) read out by a SiPM array (8 × 8 channels, 3 × 3 mm2 active area/channel and 50 μm microcell size) with data acquisition, signal processing and digitization performed using the PETsys Electronics Evaluations kit (based on the TOFPET v2c ASIC) builds a DOI LYSO detector block. The performance of the DOI detector was evaluated in terms of crystal resolvability, energy resolution, and coincidence resolving time (CRT). A comparative performance evaluation of the staggered three-layer LYSO block was conducted with two different SiPM arrays from KETEK and HAMAMATSU. 100% (KETEK) and 99.8% (HAMAMATSU) of the crystals were identified, by using a flood irradiation the front- and back-side. The average energy resolutions for the 1st, 2nd, and 3rd layers were 16.5 (±2.3)%, 20.9(±4.0)%, and 32.7 (±21.0)% (KETEK) and 19.3 (±3.5)%, 21.2 (±4.1)%, and 26.6 (±10.3)% (HAMAMATSU) for the used SiPM arrays. The measured CRTs (FWHM) for the 1st, 2nd, and 3rd layers were 532 (±111) ps, 463 (±108) ps, and 447 (±111) ps (KETEK) and 402 (±46) ps, 392 (±54) ps, and 408 (±196) ps (HAMAMATSU). In conclusion, the performance of the staggered three-layer DOI detector with 1 mm LYSO pitch and 19.8 mm total crystal thickness was fully characterized. The feasibility of a highly performing readout of a high resolution DOI PET detector via SiPM arrays from KETEK and HAMAMATSU employing the PETsys TOFPET v2c ASIC could be demonstrated.

Highlights

  • In recent years the effort to improve the spatial resolution and quality of PET imaging systems has steadily increased

  • A KETEK PA3350WB-0808 prototype silicon photomultipliers (SiPMs) array with a breakdown voltage of 25.2 V (5.0 V recommended overvoltage/30.2 V applied voltage) and a HAMAMATSU S14161-3050HS-08 MPPC array with a breakdown voltage of 38.6 V (2.7 V recommended overvoltage/41.3 V applied voltage) (HAMAMATSU Photonics K.K 2020) were used

  • For the studies presented in this work SiPM/MPPC arrays from two manufacturers (KETEK and HAMAMATSU) have been investigated and compared

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Summary

Introduction

In recent years the effort to improve the spatial resolution and quality of PET imaging systems has steadily increased. The first commercially used TOF PET scintillators (CsF and BaF2, 1-to-1 coupled to PMTs) could achieve TOF capabilities between 470 and 750 ps They were still suffering from low light yield and low material densities, resulting in limited detection efficiency and spatial resolution, the latter due to the large crystal sizes required (Melcher 2000, Surti and Karp 2016, Conti and Bendriem 2019, Saint-Gobain Crystals 2020a). Nowadays modern scintillation crystals such as LSO and LYSO, in combination with silicon photomultipliers (SiPMs) and dedicated signal processing electronics, allow for coincidence resolving times (CRT) of commercial systems to reach close to 200 ps (Surti 2015, Reddin et al 2018, Conti and Bendriem 2019, van Sluis et al 2019), while providing high detection efficiencies due to their high Z and density (Saint-Gobain Crystals 2020b) and high spatial resolution (e.g. by using an Anger-type detector readout). The ultimate goal targets a CRT of about 10 ps (Grundacker et al 2019), which would allow to directly obtain the β+-annihilation position by measuring the detection time difference with an accuracy that is similar to the current reconstruction methods that rely on the intersection of the linesof-response (LOR) of multiple detected positron annihilation photon pairs (Lecoq et al 2020)

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