Design and measurement of Trans-PET basic detector module II using 6× 6 SiPM array for small-animal PET

Niu, Muye; Cheng, Hua; Liu, T; Yang, Yanchao; Xie, Qiangqiang; Xiao, Peng

doi:10.1088/1748-0221/15/09/p09040

Cited by 4 publications

(4 citation statements)

References 44 publications

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“…Recently, a lot of work has been done in developing dual‐ended readout PET detectors using silicon photomultiplier (SiPM) 25–28 . SiPM is an ideal or preferred photodetector for dual‐ended readout PET detectors due to its compact size, high quantum efficiency, high gain, low dark current, good timing performance, good magnetic resonance imaging compatibility, wide availability, and low cost 29–32 …”

Section: Introductionmentioning

confidence: 99%

“…[25][26][27][28] SiPM is an ideal or preferred photodetector for dualended readout PET detectors due to its compact size, high quantum efficiency, high gain, low dark current, good timing performance, good magnetic resonance imaging compatibility, wide availability, and low cost. [29][30][31][32] The spatial resolution of current commercial small animal PET scanners is far worse than the physical limit. Hence, the development of PET detectors and scanners with a resolution of about 0.5 mm has been an important direction of PET instrumentation, especially for dedicated mouse PET imaging.…”

Section: Introductionmentioning

confidence: 99%

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Ultra‐high‐resolution depth‐encoding small animal PET detectors: Using GAGG and LYSO crystal arrays

et al. 2022

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Purpose Small animal positron emission tomography (PET) scanners are widely used in current biomedical research. The study aimed to develop high‐efficiency and ultra‐high‐resolution detectors that could be used to develop a small animal PET scanner with high sensitivity and spatial resolution approaching to its physical limit. Methods Four crystal arrays were fabricated and measured in this study. Crystal arrays 1 and 2 consisted of 38 × 38 gadolinium aluminum gallium garnet (GAGG) and lutetium–yttrium oxyorthosilicate (LYSO) crystals of 0.4 × 0.4 × 20 mm3 size. Crystal array 3 consisted of 16 × 16 GAGG crystals of 0.3 × 0.3 × 20 mm3 size, and crystal array 4 consisted of 24 × 24 LYSO crystals 0.3 × 0.3 × 20 mm3 in size. The crystal arrays were dual‐ended readouts using 8 × 8 silicon photomultiplier (SiPM) arrays of 2 × 2 mm2 pixel area. The SiPM array was readout using a signal multiplexing circuit to convert the 64 output signals into four position‐encoding signals. The performances of the four detectors in terms of flood histogram, energy resolution, depth of interaction (DOI) resolution, and timing resolution were measured. Results The GAGG detectors provided better flood histograms, ∼30% higher photopeak amplitude, ∼20% higher energy resolution, ∼12% worse DOI resolution, and ∼15% worse timing resolution compared with LYSO detectors of the same crystal size. These four detectors provided DOI resolutions of <2 mm, energy resolutions of <22%, and timing resolutions of <1.6 ns. All crystals of 0.4 × 0.4 × 20 mm3 and 0.3 × 0.3 × 20 mm3 could be clearly resolved if the crystal array was 1 mm smaller in the four sides than that in the SiPM array. Conclusions High DOI resolution PET detectors were developed using both GAGG and LYSO arrays with crystal sizes of 0.3 and 0.4 mm, respectively, and a length of 20 mm. The detectors can be used in the future to develop small animal PET scanners, especially dedicated mouse imaging PET scanners, which can simultaneously achieve high sensitivity and ultra‐high spatial resolution.

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Section: Introductionmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

Ultra‐high‐resolution depth‐encoding small animal PET detectors: Using GAGG and LYSO crystal arrays

et al. 2022

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“…It is composed of two planar detector heads with a detection area of 216 mm×145.5 mm, which are mounted at a distance of 120 mm. Each head consists of 2×5 Trans-PET basic detector modules (BDMs) (Hua et al 2018;Niu et al 2020) developed by Raycan Technology Co., Ltd (Suzhou). A total of 20 BDMs without depth of interaction (DOI) hardware are connected to a global clock module, which sends a time synchronization command before acquisition.…”

Section: Methodsmentioning

confidence: 99%

DH-Mammo PET: a dual-head positron emission mammography system for breast imaging

Shi¹,

Wang²,

Zhou³

et al. 2022

Phys. Med. Biol.

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Objective: To develop a simultaneous PET-Optical (OPET) breast imaging dual-head PET subsystem, called DH-Mammo PET, for accurate, early diagnosis and efficacy assessment of breast cancer with high resolution and sensitivity. Approach: We developed a breast-dedicated PET based on LYSO crystal, silicon photomultiplier array and multi-voltage threshold sampling technique. It consists of two detector heads, each with a detection area of 216 mm × 145.5 mm. The distance between the detector heads is fixed at 120 mm. In order to extract coincidences and correct data, GPU-based software coincidence processing, random, scatter, normalization, gap-filling and attenuation corrections were applied in turn. The images were reconstructed using maximum likelihood expectation maximization with depth of interaction (DOI) modeling. The performance of DH-Mammo PET was evaluated referring to NEMA NU 4-2008, NU 2-2007 and Chinese industry recommended standard YY/T 1835-2022. Besides, several clinical patient images of DH-Mammo PET were compared with those of a whole-body PET/CT. Main results: The energy resolution was 14.5%, and time resolution was < 1.31 ns. Indicated by the 22Na point source imaging, its spatial resolution was 2.60 mm (5.40 mm), 1.00 mm (1.04 mm), and 0.96 mm (0.93 mm) in the X, Y and Z directions, respectively, using the system response matrix with (without) DOI modeling. Indicated by the Derenzo phantom imaging, the spatial resolution was ~3.0 mm, <1.2 mm, and <1.2 mm in the X, Y and Z directions. The system sensitivity was 6.87%, 4.89% and 3.37% with an energy window of 100-800, 250-750 and 350-650 keV, respectively. The scatter fraction was 26.43%, and the peak NECR was 162.6 kcps at 24.1 MBq for the modified rat-like phantom. As for the recovery coefficients, they ranged from 0.15 to 1.04 for rods between 1 mm and 5 mm obtained with a NEMA image quality phantom. The spill-over ratio for the air-filled and water-filled chamber was 0.05 and 0.11, respectively. DH-Mammo PET can provide more image details in clinical experiments and fulfil a fast scan with 60s-120 s acquisition time. Significance: Good spatial resolution and high sensitivity of DH-Mammo PET would enable fast and accurate PET imaging of the breast. Besides, combining the DH-Mammo PET with the diffuse optical tomography would make full use of tumor metabolic imaging and tissue endogenous optical imaging, which would improve the accuracy of early clinical diagnosis of small lesions of breast cancers.

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“…A PET detector module needs to measure the arrival time, energy and position of the incident 511 keV photon. To identify the tiny scintillator elements for high spatial resolution, a general PET scanner requires tens of thousands of readout channels [7][8]. Power consumption and density become challenging issues when the readout electronics system scales up [9].…”

Section: Introduction Owadays Positron Emission Computed Tomography (...mentioning

confidence: 99%

Design and Evaluation of an FPGA-ADC Prototype for the PET Detector Based on LYSO Crystals and SiPM Arrays

Ma¹,

Dong

Yu³

et al. 2022

IEEE Trans. Radiat. Plasma Med. Sci.

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the aim of this study is to design and evaluate a simple free running Analog-Digital Converter (ADC) based on the Field Programmable Gate Array (FPGA) device to accomplish the energy and position readout of the silicon photomultiplier (SiPM) array for application as PET scanners. This simple FPGA-ADC based on a carry chain Time-Digital Converter (TDC) implemented on a Kintex-7 FPGA consists of only one off-chip resistor so it has greater advantages in improving system integration and reducing cost than commercial chips. In this paper, a FPGA-ADC based front-end electronics prototype is presented, and both the design principle and implementation considerations are discussed. Experiments were performed using an 8 × 8 (crystal size: 4 × 4 × 15 mm 3 ) and a 12 × 12 (crystal size: 2.65 × 2.65 × 15 mm 3 ) segmented LYSO crystals coupled with an 8 × 8 SiPM (Jseries, from ON Semiconductor) array which is under 22 Na point source excitation. Initial test results indicate that the energy resolution of the two detectors after correction is around 13.2% and 13.5 % at 511 keV, and the profiles of the flood histograms show a clear visualization of the discrete scintillator element. All measurements were carried out at room temperature (~25 °C), without additional cooling.

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Design and measurement of Trans-PET basic detector module II using 6× 6 SiPM array for small-animal PET

Cited by 4 publications

References 44 publications

Ultra‐high‐resolution depth‐encoding small animal PET detectors: Using GAGG and LYSO crystal arrays

Ultra‐high‐resolution depth‐encoding small animal PET detectors: Using GAGG and LYSO crystal arrays

DH-Mammo PET: a dual-head positron emission mammography system for breast imaging

Design and Evaluation of an FPGA-ADC Prototype for the PET Detector Based on LYSO Crystals and SiPM Arrays

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