Design and performance evaluation of a compact, large-area PET detector module based on silicon photomultipliers

Wang, Yingjie; Zhang, Zhiming; Li, Daowu; Wang, Baoyi; Shuai, Lei; Feng, Baojie; Chai, Peiqi; Liu, Shuangquan; Tang, Haina; Li, Ting; Liao, Yanfei; Huang, Xianchao; Yan, Chuanwei; Liu, Yantao; Zhang, Yiwen; Wei, Long

doi:10.1016/j.nima.2011.12.064

Cited by 21 publications

(12 citation statements)

References 12 publications

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“…Thus, the active area of the detector is 41.2 × 91.5 mm 2 , which is larger than other SiPM-based detector modules reported in the literature (Chagani 2009, Schaart 2009, Yamamoto 2010, Llosa 2011, Zorzi 2011,Schulz 2011, Wang 2012, Yoon 2012). The LYSO array was coupled to two SensL ArraySL-4p9s (SensL Technologies, LTD., Cork Ireland).…”

Section: Methodsmentioning

confidence: 77%

“…These devices have higher gain than APDs, comparable to photomultiplier tubes (on the order of 1x10 6 ), and have the same insensitivity to magnetic fields as APDs (Roncali and Cherry 2011). A number of investigators have created MR-compatible PET detector modules from which MRI-PET scanners can be constructed (Chagani 2009, Schaart 2009, Yamamoto 2010, Llosa 2011, Schulz 2011, Zorzi 2011,Wang 2012, Yoon 2012). For example, a group from the Seoul National University constructed a 32.4 × 28.7 mm 2 SiPM-based PET detector module (Yoon 2012).…”

Section: Introductionmentioning

confidence: 99%

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A large area, silicon photomultiplier-based PET detector module

Raylman

Stolin

Majewski

et al. 2014

Nuclear Instruments and Methods in Physics Research Section A:

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The introduction of silicon photomultipliers (SiPM) has facilitated construction of compact, efficient and magnetic field-hardened positron emission tomography (PET) scanners. To take full advantage of these devices, methods for using them to produce large field-of-view PET scanners are needed. In this investigation, we explored techniques to combine two SiPM arrays to form the building block for a small animal PET scanner. The module consists of a 26 × 58 array of 1.5 × 1.5mm2 LYSO elements (spanning 41 × 91mm2) coupled to two SensL SiPM arrays. The SiPMs were read out with new multiplexing electronics developed for this project. To facilitate calculation of event position with multiple SiPM arrays it was necessary to spread scintillation light amongst a number of elements with a small light guide. This method was successful in permitting identification of all detector elements, even at the seam between two SiPM arrays. Since the performance of SiPMs is enhanced by cooling, the detector module was fitted with a cooling jacket, which allowed the temperature of the device and electronics to be controlled. Testing demonstrated that the peak-to-valley contrast ratio of the light detected from the scintillation array was increased by ∼45% when the temperature was reduced from 28 °C to 16 °C. Energy resolution for 511 keV photons improved slightly from 18.8% at 28 °C to 17.8% at 16 °C. Finally, the coincidence timing resolution of the module was found to be insufficient for time-of-flight applications (∼2100 ps at 14 °C). The first use of these new modules will be in the construction of a small animal PET scanner to be integrated with a 3T clinical magnetic resonance imaging scanner.

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Section: Methodsmentioning

confidence: 77%

Section: Introductionmentioning

confidence: 99%

A large area, silicon photomultiplier-based PET detector module

Raylman

Stolin

Majewski

et al. 2014

Nuclear Instruments and Methods in Physics Research Section A:

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“…A row-column readout of the SiPM matrix was used without applying individual signalprocessing channels to each matrix element. Weighting circuits were connected directly to the row and column outputs as proposed by Wang et al (13) but modified to reduce the dark noise. The overlap between the crystals and the SiPM-sensitive areas was determined during design of the SiPM sensors to optimize position encoding.…”

Section: System Descriptionmentioning

confidence: 99%

“…System peak absolute sensitivity is defined as the S A,i at the center of the field of view (13). Total absolute sensitivity (S A,tot ) was calculated using the following equation:…”

Section: Sensitivitymentioning

confidence: 99%

A Promising Future: Comparable Imaging Capability of MRI-Compatible Silicon Photomultiplier and Conventional Photosensor Preclinical PET Systems

et al. 2015

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We recently completed construction of a small-animal PET systemthe MiniPET-3-that uses state-of-the-art silicon photomultiplier (SiPM) photosensors, making possible dual-modality imaging with MRI. In this article, we compare the MiniPET-3 with the MiniPET-2, a system with the same crystal geometry but conventional photomultiplier tubes (PMTs). Methods: The standard measurements proposed by the National Electrical Manufacturers Association NU 4 protocols were performed on both systems. These measurements included spatial resolution, system sensitivity, energy resolution, counting rate performance, scatter fraction, spillover ratio for air and water, recovery coefficient, and image uniformity. The energy windows were set to 350-650 keV on the MiniPET-2 and 360-662 keV on the MiniPET-3. Results: Spatial resolution was approximately 17% better on average for the MiniPET-3 than the MiniPET-2. The systems performed similarly in terms of peak absolute sensitivity (∼1.37%), spillover ratio for air (∼0.15), spillover ratio for water (∼0.25), and recovery coefficient (∼0.33, 0.59, 0.81, 0.89, and 0.94). Uniformity was 5.59% for the MiniPET-2 and 6.49% for the MiniPET-3. Minor differences were found in scatter fraction. With the ratlike phantom, the peak noise-equivalent counting rate was 14 kcps on the MiniPET-2 but 24 kcps on the MiniPET-3. However, with the mouselike phantom, these values were 55 and 91 kcps, respectively. The optimal coincidence time window was 6 ns for the MiniPET-2 and 8 ns for the MiniPET-3. Conclusion: Images obtained with the SiPM-based Mini-PET-3 small-animal PET system are similar in quality to those obtained with the conventional PMT-based MiniPET-2.Key Words: MiniPET; small-animal PET scanner; performance evaluation; instrumentation; molecular imaging J Nucl Med 2015; 56:1948 56: -1953 56: DOI: 10.2967 Ef forts to integrate PET and MRI have advanced significantly in recent years, fostered mainly by new photosensor technologies (1-4). Conventional photomultiplier tube (PMT) detectors benefit from high signal gain in the range of 10 5 -10 7 (5,6). Low noise and fast transit time (;100 ps) are also available today and have made PMTs the first candidate for applications involving time-of-flight PET technology. In addition, PMTs have lower noise than avalanche photodiode or silicon photomultiplier (SiPM) detectors (5). However, in strong magnetic fields PMTs cannot produce position maps that are acceptable for imaging purposes. In contrast, avalanche photodiodes can be used efficiently as a photosensor for PET when near strong magnets. Some successful approaches using avalanche photodiodes have already been introduced for combined PET/MRI applications (2,7,8). However, avalanche photodiodes have significantly higher rise times than PMTs (up to 2-3 ns) (5), preventing the timing resolution from being adequate for time-of-flight PET. The low gain (;10 2 ) is also a disadvantage of avalanche photodiodes (2,5).By coupling lutetium oxyorthosilicate crystals with new SiPM technology, a timing resolutio...

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“…Because the size of an individual SiPM is usually small (i.e. or less), many designs combine arrays of SiPMs to make detector modules with larger surface areas [1]- [3]. Often the signals from these SiPMs are multiplexed to reduce the number of data lines leaving each module [4]- [6].…”

Section: Introductionmentioning

confidence: 99%

Multiplexing Approaches for a 12 x 4 Array of Silicon Photomultipliers

Liu

Goertzen

2014

IEEE Trans. Nucl. Sci.

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Two resistor network multiplexing circuits for a 12 4 array of SiPMs were constructed and tested. Both circuits encode the position and energy information from 48 SiPM pixels in only 4 analog channels. The two circuits differ in that one buffers each SiPM output with a non-inverting voltage-feedback operational amplifier before multiplexing, whereas the second one connects the output of the SiPMs directly to a charge division resistor network. The energy and timing resolution were measured with a 4 4 array of LYSO scintillator crystals with size matched to the SiPM pixel size. The measurement was done in 3 steps to cover all 12 4 SiPMs. Both circuits gave an energy resolution of 14%. The single sided timing resolution for the buffered output circuit was 2.86 ns, using a 350-650 keV energy window. In comparison, the timing for the circuit with direct connections between SiPMs and the resistor network was 3.54 ns, using the same energy window. Based on these results, the predicted coincidence timing resolutions are 4.0 ns and 5.0 ns, respectively. The coupling of the SiPM capacitance with the resistor network results in different signal shaping time constants for different SiPMs in the passive resistor network, causing a delay in trigger time for the inner SiPM signals. On the other hand, the circuit with buffer amplifiers does not suffer from this effect, and the pulse shape is more uniform across the SiPMs. We also demonstrate, using a 10 10 array of 1.5 mm LYSO crystals, that the inclusion of multiple SiPMs in both circuits reduces the detector's ability to resolve crystals in the flood histograms. The amount of noise increases with number of SiPMs in the multiplexing circuit.Index Terms-Positron emission tomography, signal multiplexing, silicon photomultiplier.

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Design and performance evaluation of a compact, large-area PET detector module based on silicon photomultipliers

Cited by 21 publications

References 12 publications

A large area, silicon photomultiplier-based PET detector module

A large area, silicon photomultiplier-based PET detector module

A Promising Future: Comparable Imaging Capability of MRI-Compatible Silicon Photomultiplier and Conventional Photosensor Preclinical PET Systems

Multiplexing Approaches for a 12 x 4 Array of Silicon Photomultipliers

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