Highly multiplexed SiPM signal readout for brain-dedicated TOF-DOI PET detectors

Park, Haewook; Lee, Jae Sung

doi:10.1016/j.ejmp.2019.11.016

Cited by 25 publications

(13 citation statements)

References 31 publications

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“…The high-performance TDC with the LSB size of 16 ps and a low-jitter clock distribution system through 20-m HDMI cables enabled the system-level timing uncertainty of 17.0 ps. Although the DAQ systems have a low timing uncertainty of 17.0 ps, the CTR value of approximately 500 ps FWHM was worse than that in our previous detector-level study [47], where we achieved the CTR values of 336 and 347 ps FWHM for upper-and lower-layer crystals, respectively. We consider that the narrow spacing between the fast timing signals due to the highly integrated circuit design of the current block detector degraded the timing resolution.…”

Section: Discussioncontrasting

confidence: 79%

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Development and Initial Results of a Brain PET Insert for Simultaneous 7-Tesla PET/MRI Using an FPGA-Only Signal Digitization Method

Won

Park

Lee

et al. 2021

IEEE Trans. Med. Imaging

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In this study, we developed a positron emission tomography (PET) insert for simultaneous brain imaging within 7-Tesla (7T) magnetic resonance (MR) imaging scanners. The PET insert has 18 sectors, and each sector is assembled with two-layer depth-of-interaction (DOI)-capable high-resolution block detectors. The PET scanner features a 16.7-cm-long axial field-of-view (FOV) to provide entire human brain images without bed movement. The PET scanner early digitizes a large number of block detector signals at a front-end data acquisition (DAQ) board using a novel field-programmable gate array (FPGA)-only signal digitization method. All the digitized PET data from the front-end DAQ boards are transferred using gigabit transceivers via non-magnetic high-definition multimedia interface (HDMI) cables. A back-end DAQ system provides a common clock and synchronization signal for FPGAs over the HDMI cables. An active cooling system using copper heat pipes is applied for thermal regulation. All the 2.17-mm-pitch crystals with two-layer DOI information were clearly identified in the block detectors, exhibiting a system-level energy resolution of 12.6%. The PET scanner yielded clear hot-rod and Hoffman brain phantom images and demonstrated 3D PET imaging capability without bed movement. We also performed a pilot simultaneous PET/MR imaging study of a brain phantom. The PET scanner achieved a spatial resolution of 2.5 mm at the center FOV (NU 4) and a sensitivity of 18.9 kcps/MBq (NU 2) and 6.19% (NU 4) in accordance with the National Electrical Manufacturers Association (NEMA) standards.

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Section: Discussioncontrasting

confidence: 79%

“…The cross-sectional area of the block detector is 26.2 × 26.2 mm 2 . Further, the 64 SiPM anode signals are reduced into the four energy signals using a resistive charge division circuit[46,47]. The common cathode signal is used as a timing signal.…”

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confidence: 99%

Development and Initial Results of a Brain PET Insert for Simultaneous 7-Tesla PET/MRI Using an FPGA-Only Signal Digitization Method

Won

Park

Lee

et al. 2021

IEEE Trans. Med. Imaging

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“…In order to reduce the cost of the SiPM array and crystals and the complexity of the readout circuit, a SiPM unit is usually coupled with multiple crystals and a multiplexing method is utilized to reduce the readout channels. At the same time, the time performance of the detector is deteriorated [ 29 , 30 , 31 , 32 ].…”

Section: Introductionmentioning

confidence: 99%

Design and Evaluation of LYSO/SiPM LIGHTENING PET Detector with DTI Sampling Method

Deng

Chen

2020

Sensors

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Positron emission tomography (PET) has a wide range of applications in the treatment and prevention of major diseases owing to its high sensitivity and excellent resolution. However, there is still much room for optimization in the readout circuit and fast pulse sampling to further improve the performance of the PET scanner. In this work, a LIGHTENING® PET detector using a 13 × 13 lutetium-yttrium oxyorthosilicate (LYSO) crystal array read out by a 6 × 6 silicon photomultiplier (SiPM) array was developed. A novel sampling method, referred to as the dual time interval (DTI) method, is therefore proposed to realize digital acquisition of fast scintillation pulse. A semi-cut light guide was designed, which greatly improves the resolution of the edge region of the crystal array. The obtained flood histogram shown that all the 13 × 13 crystal pixels can be clearly discriminated. The optimum operating conditions for the detector were obtained by comparing the flood histogram quality under different experimental conditions. An average energy resolution (FWHM) of 14.3% and coincidence timing resolution (FWHM) of 972 ps were measured. The experimental results demonstrated that the LIGHTENING® PET detector achieves extremely high resolution which is suitable for the development of a high performance time-of-flight PET scanner.

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“…A few ASICs have been developed to read the output of 16-64 SiPMs in time-of-flight Positron Emission Tomography (TOF PET) applications, which do not perform the sum of the signals but output a number of digital/binary signals equal to the number of inputs (see for instance [31,32]). However, reducing the number of readout channels is often also desirable in PET, as can be seen in [33,34]. The requirements for the electronics of TOF PET are in principle more demanding than in PET, since high-precision timing and some information on the single-SiPM charge to estimate the depth of interaction of gamma rays inside the crystal are needed.…”

Section: Lasip Size and Geometrymentioning

confidence: 99%

Large-Area SiPM Pixels (LASiPs): a cost-effective solution towards compact large SPECT cameras

Guberman,

Paoletti,

Rugliancich

et al. 2021

Preprint

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Single Photon Emission Computed Tomography (SPECT) scanners based on photomultiplier tubes (PMTs) are still largely employed in the clinical environment. A standard camera for full-body SPECT employs ∼ 50-100 PMTs of 4-8 cm diameter and is shielded by a thick layer of lead, becoming a heavy and bulky system that can weight a few hundred kilograms. The volume, weight and cost of a camera can be significantly reduced if the PMTs are replaced by silicon photomultipliers (SiPMs). The main obstacle to use SiPMs in full-body SPECT is the limited size of their sensitive area. A few thousand channels would be needed to fill a camera if using the largest commercially-available SiPMs of 6×6 mm 2 . As a solution, we propose to use Large-Area SiPM Pixels (LASiPs), built by summing individual currents of several SiPMs into a single output. We developed a LASiP prototype that has a sensitive area 8 times larger than a 6×6 mm 2 SiPM. We built a proof-of-concept micro-camera consisting of a 40×40×8 mm 3 NaI(Tl) crystal coupled to 4 LASiPs.We evaluated its performance in a central region of 15 × 15 mm 2 , where we were able to reconstruct images of a 99m Tc capillary with an intrinsic spatial resolution of ∼ 2 mm and an energy resolution of ∼ 11.6% at 140 keV. We used these measurements to validate Geant4 simulations of the system. This can be extended to simulate a larger camera with more and larger pixels, which could be used to optimize the implementation of LASiPs in large SPECT cameras. We provide some guidelines towards this implementation.

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Highly multiplexed SiPM signal readout for brain-dedicated TOF-DOI PET detectors

Cited by 25 publications

References 31 publications

Development and Initial Results of a Brain PET Insert for Simultaneous 7-Tesla PET/MRI Using an FPGA-Only Signal Digitization Method

Development and Initial Results of a Brain PET Insert for Simultaneous 7-Tesla PET/MRI Using an FPGA-Only Signal Digitization Method

Design and Evaluation of LYSO/SiPM LIGHTENING PET Detector with DTI Sampling Method

Large-Area SiPM Pixels (LASiPs): a cost-effective solution towards compact large SPECT cameras

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