Design and simulation of a novel method for determining depth-of-interaction in a PET scintillation crystal array using a single-ended readout by a multi-anode PMT

Ito, Mikiko; Lee, Jae Sung; Park, Min-Jae; Sim, K. S.; Hong, S. J.

doi:10.1088/0031-9155/55/13/017

Cited by 48 publications

(40 citation statements)

References 30 publications

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“…Several groups have shown that depth-ofinteraction encoding with SiPM is feasible (13). Implementing the depth-of-interaction encoding methods suggested by our group (14,16,32) will also be possible using the SiPM arrays.…”

Section: Discussionmentioning

confidence: 96%

Development of Small-Animal PET Prototype Using Silicon Photomultiplier (SiPM): Initial Results of Phantom and Animal Imaging Studies

Kwon¹,

Lee²,

Yoon³

et al. 2011

J Nucl Med

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Silicon photomultiplier (SiPM; also called a Geiger-mode avalanche photodiode) is a promising semiconductor photosensor in PET and PET/MRI because it is intrinsically MRI-compatible and has internal gain and timing properties comparable to those of a photomultiplier tube. In this study, we have developed a smallanimal PET system using SiPMs and lutetium gadolinium oxyorthosilicate (LGSO) crystals and performed physical evaluation and animal imaging studies to show the feasibility of this system. Methods: The SiPM PET system consists of 8 detectors, each of which comprises 2 · 6 SiPMs and 4 · 13 LGSO crystals. Each crystal has dimensions of 1.5 · 1.5 · 7 mm. The crystal face-toface diameter and axial field of view are 6.0 cm and 6.5 mm, respectively. Bias voltage is applied to each SiPM using a finely controlled voltage supply because the gain of the SiPM strongly depends on the supply voltage. The physical characteristics were studied by measuring energy resolution, sensitivity, and spatial resolution. Various mouse and rat images were obtained to study the feasibility of the SiPM PET system in in vivo animal studies. Reconstructed PET images using a maximum-likelihood expectation maximization algorithm were coregistered with animal CT images. Results: All individual LGSO crystals within the detectors were clearly distinguishable in flood images obtained by irradiating the detector using a 22 Na point source. The energy resolution for individual crystals was 25.8% 6 2.6% on average for 511-keV photopeaks. The spatial resolution measured with the 22 Na point source in a warm background was 1.0 mm (2 mm off-center) and 1.4 mm (16 mm off-center) when the maximum-likelihood expectation maximization algorithm was applied. A myocardial 18 F-FDG study in mice and a skeletal 18 F study in rats demonstrated the fine spatial resolution of the scanner. The feasibility of the SiPM PET system was also confirmed in the tumor images of mice using 18 F-FDG and 68 Ga-RGD and in the brain images of rats using 18 F-FDG. Conclusion: These results indicate that it is possible to develop a PET system using a promising semiconductor photosensor, which yielded reasonable PET performance in phantom and animal studies.

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Section: Discussionmentioning

confidence: 96%

Development of Small-Animal PET Prototype Using Silicon Photomultiplier (SiPM): Initial Results of Phantom and Animal Imaging Studies

Kwon¹,

Lee²,

Yoon³

et al. 2011

J Nucl Med

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“…12a) [70]. This 2D light dispersion can increase the contrast of DOI dependency along the DOI position than the 1D light dispersion.…”

Section: Continuous Doi Measurement By Single-ended Readoutmentioning

confidence: 95%

Positron emission tomography (PET) detectors with depth-of- interaction (DOI) capability

2011

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Because positron emission tomography (PET) provides biochemical information in vivo with the sensitivity at the sub-pico-molar level, pre-clinical research using PET plays an important role in biological and pharmaceutical sciences. However, small animal imaging by PET has been challenging with respect to spatial resolution and sensitivity due to the small volume of the imaging objects. A DOI-encoding technique allows for pre-clinical PET to simultaneously achieve high spatial resolution and high sensitivity. Thus many DOI-encoding methods have been proposed. In this paper we describe why DOI measurements are important, what is required in DOI-encoding designs, and how to extract DOI information in scintillator-based DOI detectors. Recently, there has been a growing interest in DOI measurements for TOF PET detectors to correct time walk as a function of DOI position. Thus, the DOI-encoding method with a high time performance suitable for TOF detectors is now required. The requirements to improve the time resolution in DOI detectors are discussed as well.Keywords Positron emission tomography (PET), Depth of interaction (DOI), Multi-layer detector, Dual-ended readout, Single-ended readout THE IMPORTANCE OF DOI MEASUREMENT Simultaneous improvement in spatial resolution and sensitivityThe PET is an important pre-clinical imaging technique because PET provides biochemical information down to the sub-pico-molar level in vivo [1]. Thus, the development of pre-clinical PET scanners has been actively promoted. The major focus of the development is to obtain a similar quality in small animal images as human images, while the size of the imaging subject decreases and the amount of radiopharmaceutical injected into the small animals is limitedTo obtain a similar level of detail and SNR in mouse images as human images, spatial resolution and sensitivity should be increased. That is why many PET instrument researchers have been attempting for the pre-clinical PET to simultaneously achieve high spatial resolution and high sensitivity. The pre-clinical PET systems therefore have been designed by using very long and narrow crystals with small diameter ring geometry. However, such system structures cause the parallax error to become lager when providing no depth-of-interaction (DOI) information within crystals (general PETs can measure no DOI information), and bring the degradation of the radial resolution in the peripheral field of view (FOV). That is because the reconstruction algorithm, when drawing a line of response (LOR) without DOI information, usually assigns the interaction positions over all depths within a crystal to a single position (i.e. the center position on the front of the interacted crystals).

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“…The data loss is especially significant if we employ flat panel photomultiplier tubes or multiple layers of scintillation crystals for depth of interaction measurement. 32,[34][35][36][37][38] The conventional iterative reconstruction methods (without TV minimization) produced considerable artifacts in the reconstructed images from the gapped sinograms. To reduce the artifacts due to gaps, we applied the TV minimization to the most commonly used iterative reconstruction methods, such as ART, OSEM, and RAMLA.…”

Section: Discussionmentioning

confidence: 99%

Gap compensation during PET image reconstruction by constrained, total variation minimization

et al. 2012

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Design and simulation of a novel method for determining depth-of-interaction in a PET scintillation crystal array using a single-ended readout by a multi-anode PMT

Cited by 48 publications

References 30 publications

Development of Small-Animal PET Prototype Using Silicon Photomultiplier (SiPM): Initial Results of Phantom and Animal Imaging Studies

Development of Small-Animal PET Prototype Using Silicon Photomultiplier (SiPM): Initial Results of Phantom and Animal Imaging Studies

Positron emission tomography (PET) detectors with depth-of- interaction (DOI) capability

Gap compensation during PET image reconstruction by constrained, total variation minimization

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