A Dual-Ended Readout Detector Using a Meantime Method for SiPM TOF-DOI PET

Kang, Han Gyu; Ko, Gyung Hyuck; Rhee, J.T.; Kim, Kyeong Min; Lee, Jae Sung; Hong, S. J.

doi:10.1109/tns.2015.2449891

Cited by 53 publications

(55 citation statements)

References 26 publications

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“…The DOI measurements were achieved by comparing the differences between the signals from the two ends. Many DOI detectors based on dual‐ended readout have been developed since then . The major disadvantage of the dual‐ended readout method is that one detector requires two photosensors and readout electronics.…”

Section: Introductionmentioning

confidence: 99%

A depth encoding PET detector using four‐crystals‐to‐one‐SiPM coupling and light‐sharing window method

et al. 2019

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Purpose Depth of interaction (DOI) decoding capability is of great importance for positron emission tomography (PET) requiring high resolution. In this study, we presented a novel low‐cost DOI detector design with four crystals coupling to one SiPM, based on the method of rectangular light‐sharing window (RLSW). A prototype detector was constructed, calibrated, and assessed using the methods of homogeneous radiation and flood map analysis. Methods The DOI detector was constructed with a 4 × 4 array of lutetium‐yttrium oxyorthosilicate (LYSO) crystals (2.95 mm × 2.95 mm × 20 mm3), barium sulfate (BaSO4) reflectors, and optical glues. A RLSW 7 mm in height was deployed in the BaSO4 reflectors. A non‐DOI detector with identical dimensions and without RLSW was also constructed for comparison. The light‐output surface of the detector was air‐coupled with a 4 × 4 array of SiPMs (3 mm × 3 mm2). The signals generated from the 16 SiPMs were read out by a custom‐designed electronic system, and the signals from four adjacent 3 mm SiPMs were summed into one signal to emulate a 2 × 2 array of 6 mm SiPMs. The RLSW caused the DOI‐related position shifts of the crystal spots in the flood map. A homogeneous radiation method was used to establish the transfer functions to convert the spot shifts measured from the flood map into DOI measurements. The accuracy of the DOI measurements was assessed with data acquired using the conventional collimated radiation method. Results All 16 crystals are distinctly separated from each other in the flood map. Twelve crystals, including four central crystals and eight edge crystals, have the DOI capability. The full width half maximum (FWHM) of the DOI measurements of the central crystals and the edge crystals are 3.06 ± 0.08 and 3.79 ± 0.15 mm, respectively, for the configuration with four crystals coupling to one SiPM. By contrast, the FWHMs (3.98 ± 0.16 and 5.12 ± 0.38 mm, respectively) are slightly worse for the configuration with one crystal coupling to one SiPM. The average and standard deviation (STD) of the FWHM energy resolutions of the DOI detector and non‐DOI detector were 10.2% ± 0.7% and 10.7% ± 1.7%, respectively. Their FWHM coincidence timing resolutions were 197.0 ± 9.6 and 206.4 ± 13.3 ps, respectively. The RLSW had no significant impact on the energy resolutions and timing resolutions of the DOI detector. Conclusions The novel four‐crystals‐to‐one‐SiPM coupling technology is a cost‐efficient approach to construct high‐performance detector modules with DOI capability. The methods of homogeneous radiation and flood map analysis are easy to perform and of good performance. Those methods can be adapted in the clinic PET scanners to enable the capability of DOI measurements.

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Section: Introductionmentioning

confidence: 99%

A depth encoding PET detector using four‐crystals‐to‐one‐SiPM coupling and light‐sharing window method

et al. 2019

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“…There is no problem for iterative image reconstruction which can accurately model the system geometry . The advantage of dual‐ended readout detector is that small crystals can be resolved, a good DOI resolution can be obtained, long crystal of 20 mm or more can be used and the timing resolution may be also better than single‐ended readout detector . Among all the depth encoding PET detector techniques, dual‐ended readout detector has the greatest potential to be used to build small animal PET scanners that simultaneously achieve high spatial resolution and high sensitivity.…”

Section: Introductionmentioning

confidence: 99%

“…Clinic whole body PET scanners and preclinical PET scanners were already built with SiPM based detectors . But so far only a few studies were done on dual‐ended readout PET detector development with SiPMs and all of those studies used crystal size of 1.5 mm or bigger . The focus of this work is to develop high resolution, high efficient and high DOI resolution small animal PET detectors using dual‐ended readout of pixelated LYSO arrays optically coupled with SiPM arrays.…”

Section: Introductionmentioning

confidence: 99%

Development of depth encoding small animal PET detectors using dual‐ended readout of pixelated scintillator arrays with SiPMs

et al. 2017

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“…Experimental measurements show that this dependence is nearly linear, that the difference of the two photodetector outputs can be used to measure the DOI, and that the sum can be used to measure the energy deposited (Yang et al 2006, Ren et al 2014, Kang et al 2015, Seifert and Schaart 2015). …”

Section: Introductionmentioning

confidence: 99%

Monte Carlo simulations of time-of-flight PET with double-ended readout: calibration, coincidence resolving times and statistical lower bounds

Derenzo

2017

Phys. Med. Biol.

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This paper demonstrates through Monte Carlo simulations that a practical positron emission tomograph with (1) deep scintillators for efficient detection, (2) double-ended readout for depth-of-interaction information, (3) fixed-level analog triggering, and (4) accurate calibration and timing data corrections can achieve a coincidence resolving time (CRT) that is not far above the statistical lower bound. One Monte Carlo algorithm simulates a calibration procedure that uses data from a positron point source. Annihilation events with an interaction near the entrance surface of one scintillator are selected, and data from the two photodetectors on the other scintillator provide depth-dependent timing corrections. Another Monte Carlo algorithm simulates normal operation using these corrections and determines the CRT. A third Monte Carlo algorithm determines the CRT statistical lower bound by generating a series of random interaction depths, and for each interaction a set of random photoelectron times for each of the two photodetectors. The most likely interaction times are determined by shifting the depth-dependent probability density function to maximize the joint likelihood for all the photoelectron times in each set. Example calculations are tabulated for different numbers of photoelectrons and photodetector time jitters for three 3 × 3 × 30 mm3 scintillators: Lu2SiO5:Ce,Ca (LSO), LaBr3:Ce, and a hypothetical ultra-fast scintillator. To isolate the factors that depend on the scintillator length and the ability to estimate the DOI, CRT values are tabulated for perfect scintillator-photodetectors. For LSO with 4000 photoelectrons and single photoelectron time jitter of the photodetector J = 0.2 ns (FWHM), the CRT value using the statistically weighted average of corrected trigger times is 0.098 ns FWHM and the statistical lower bound is 0.091 ns FWHM. For LaBr3:Ce with 8000 photoelectrons and J = 0.2 ns FWHM, the CRT values are 0.070 and 0.063 ns FWHM, respectively. For the ultra-fast scintillator with 1 ns decay time, 4000 photoelectrons, and J = 0.2 ns FWHM, the CRT values are 0.021 and 0.017 ns FWHM, respectively. The examples also show that calibration and correction for depth-dependent variations in pulse height and in annihilation and optical photon transit times are necessary to achieve these CRT values.

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A Dual-Ended Readout Detector Using a Meantime Method for SiPM TOF-DOI PET

Cited by 53 publications

References 26 publications

A depth encoding PET detector using four‐crystals‐to‐one‐SiPM coupling and light‐sharing window method

A depth encoding PET detector using four‐crystals‐to‐one‐SiPM coupling and light‐sharing window method

Development of depth encoding small animal PET detectors using dual‐ended readout of pixelated scintillator arrays with SiPMs

Monte Carlo simulations of time-of-flight PET with double-ended readout: calibration, coincidence resolving times and statistical lower bounds

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