Investigation of depth-of-interaction by pulse shape discrimination in multicrystal detectors read out by avalanche photodiodes

Saoudi, A.; Pépin, C.; Dion, F.; Bentourkin, M.; Andreacu, M.; Casey, M.; Nutt, R.; Dautet, H.

doi:10.1109/nssmic.1998.774351

Cited by 32 publications

(33 citation statements)

References 16 publications

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“…Multilayer detectors consisting of crystal layers with different scintillation light decay times (14)(15)(16), comprising different reflector arrangements (17,18), and using a position shift of half a crystal for different layers (19) have been proposed and successfully implemented to measure DOI. The DOI resolution obtained by these methods is limited by the number of layers that can be decoded and is typically 5-10 mm.…”

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confidence: 99%

A Prototype PET Scanner with DOI-Encoding Detectors

Yang¹,

Wu²,

Qi³

et al. 2008

J Nucl Med

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Detectors with depth-encoding allow a PET scanner to simultaneously achieve high sensitivity and high spatial resolution. Methods: A prototype PET scanner, consisting of depth-encoding detectors constructed by dual-ended readout of lutetium oxyorthosilicate (LSO) arrays with 2 position-sensitive avalanche photodiodes (PSAPDs), was developed. The scanner comprised 2 detector plates, each with 4 detector modules, and the LSO arrays consisted of 7 · 7 elements, with a crystal size of 0.9225 · 0.9225 · 20 mm and a pitch of 1.0 mm. The active area of the PSAPDs was 8 · 8 mm. The performance of individual detector modules was characterized. A line-source phantom and a hot-rod phantom were imaged on the prototype scanner in 2 different scanner configurations. The images were reconstructed using 20, 10, 5, 2, and 1 depth-of-interaction (DOI) bins to demonstrate the effects of DOI resolution on reconstructed image resolution and visual image quality. Results: The flood histograms measured from the sum of both PSAPD signals were only weakly depth-dependent, and excellent crystal identification was obtained at all depths. The flood histograms improved as the detector temperature decreased. DOI resolution and energy resolution improved significantly as the temperature decreased from 20°C to 10°C but improved only slightly with a subsequent temperature decrease to 0°C. A full width at half maximum (FWHM) DOI resolution of 2 mm and an FWHM energy resolution of 15% were obtained at a temperature of 10°C. Phantom studies showed that DOI measurements significantly improved the reconstructed image resolution. In the first scanner configuration (parallel detector planes), the image resolution at the center of the field of view was 0.9-mm FWHM with 20 DOI bins and 1.6-mm FWHM with 1 DOI bin. In the second scanner configuration (detector planes at a 40°angle), the image resolution at the center of the field of view was 1.0-mm FWHM with 20 DOI bins and was not measurable when using only 1 bin. Conclusion: PET scanners based on this detector design offer the prospect of high and uniform spatial resolution (crystal size, ;1 mm; DOI resolution, ;2 mm), high sensitivity (20-mm-thick detectors), and compact size (DOI encoding permits detectors to be tightly packed around the subject and minimizes number of detectors needed). Over the past decade, many small-animal PET scanners have been developed (1-12), and this technology has played a very important role in the rapidly growing field of molecular imaging. High sensitivity is needed to increase signal-to-noise ratio of the images to reliably detect lower levels of radiotracer uptake and to reduce the injected dose (reducing radiation dose to the subject) (13) and scan time (increasing temporal resolution for dynamic studies). High spatial resolution is required to detect small structures and lesions and to improve quantification by reducing the partialvolume effect. A compromise between sensitivity and spatial resolution due to depth-of-interaction (DOI) effects always exists in small-ani...

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confidence: 99%

A Prototype PET Scanner with DOI-Encoding Detectors

Yang¹,

Wu²,

Qi³

et al. 2008

J Nucl Med

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“…The top entrance size of the light-guide remains the same with the scintillator array crystal area (23.5 × 23.5 mm 2 ). The exit size of the light-guide was 20.7 × 20.7 mm 2 , the length was 10.5 mm and the reflectors was 0.1 mm BaSO 4 . This design enables all 18 × 18 scintillator array crystal to be read out on effective detection area photocathode of the PSPMT.…”

Section: Modular Construction Of the Pet Detectormentioning

confidence: 99%

“…The ideal scintillator should have the following advantages: high density, high effective atomic number, high light yield, short light decay time, and good energy resolution, etc. Many kinds of scintillation crystals have been used in PET detectors, including thallium doped with sodium iodide (NaI(Tl)), bismuth germanate (BGO), gadolinium oxyorthosilicate (GSO), lutetium oxyorthosilicate (LSO), lutetium-yttrium oxyorthosilicate (LYSO), and lanthanum [3][4][5][6]. Among these scintillators, LYSO has been the first choice in state-of-the-art PET detector design, especially in TOF-PET imaging applications.…”

Section: Introductionmentioning

confidence: 99%

Positron emission tomography detector performance with different crystal pitches

Tong

Fan

Dong

et al. 2017

Radiat Detect Technol Methods

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Aims: In this work, we evaluated the performance of three pitches positron emission tomography (PET) detectors for building a high-resolution small-animal PET imaging experimental platform. Methods: The evaluation of PET detectors includes twodimensional crystal identification, energy resolution, and crystal look-up table. The nuclear instrumentation module and PXI data acquisition (DAQ) system were both used to obtain flood images. The energy spectrum of the Na-22 source was measured. PET detectors of 2.0 and 1.6 mm pitches used in our present experiment were composed of lutetium yttrium oxyorthosilicate (LYSO) crystals directly coupled to position-sensitive photomultiplier tubes (PSPMTs). The 1.3-mm pitch detector comprises a LYSO crystal, a tapered light-guide, and a PSPMT. The crystal sizes of the detectors were a 10 × 10 array of 2.0 × 2.0 × 10 mm 3 crystals, a 10 × 10 array of 1.6 × 1.6 × 10 mm 3 crystals, and an 18×18 array of 1.3×1.3×10 mm 3 crystals, respectively. Due to the lower sampling frequency of the DAQ system, a spline interpolation algorithm was introduced in the signal waveform to reconstruct the peak values. Results: The experimental results indicated that all three PET detector crystals could be clearly identified. A detailed analysis demonstrated that the key characteristic full width at half maximum (FWHM) values of the crystals profile could reach 0.46 ± 0.03, 0.32 ± 0.03, and 0.21 ± 0.02 mm, while the crystal average energy resolutions were 16.8% ± 1.76%, 20.1% ± 2.24%, and 31.5% ± 3.76%, which correspond to B YongZhi Yin yinyzh@lzu.edu.cn 1 School of Nuclear Science and Technology, Lanzhou University, Lanzhou 730000, China pitches of 2.0-, 1.6-, and 1.3-mm, respectively. Conclusions: The PET detector modules of LYSO crystal arrays could be potentially used in the small-animal PET imaging applications and are promising to achieve submillimeter PET images.

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“…9 The DOI detector consists of a multilayered scintillator with different scintillation properties. 10,11 Moreover, a phoswich (phosphor sandwich) detector which consists of a few scintillators identifies an incident particle type by PSD analysis in a common readout, 12 and applies a background rejection method using anti-Compton analysis. 13 To evaluate the PSD performance with various detectors, it is essential that the pulse emulation reproduces the exact measured pulse.…”

Section: Introductionmentioning

confidence: 99%

Signal pulse emulation for scintillation detectors using Geant4 Monte Carlo with light tracking simulation

Ogawara

Ishikawa

2016

Review of Scientific Instruments

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The anode pulse of a photomultiplier tube (PMT) coupled with a scintillator is used for pulse shape discrimination (PSD) analysis. We have developed a novel emulation technique for the PMT anode pulse based on optical photon transport and a PMT response function. The photon transport was calculated using Geant4 Monte Carlo code and the response function with a BC408 organic scintillator. The obtained percentage RMS value of the difference between the measured and simulated pulse with suitable scintillation properties using GSO:Ce (0.4, 1.0, 1.5 mol%), LaBr3:Ce and BGO scintillators were 2.41%, 2.58%, 2.16%, 2.01%, and 3.32%, respectively. The proposed technique demonstrates high reproducibility of the measured pulse and can be applied to simulation studies of various radiation measurements

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Investigation of depth-of-interaction by pulse shape discrimination in multicrystal detectors read out by avalanche photodiodes

Cited by 32 publications

References 16 publications

A Prototype PET Scanner with DOI-Encoding Detectors

A Prototype PET Scanner with DOI-Encoding Detectors

Positron emission tomography detector performance with different crystal pitches

Signal pulse emulation for scintillation detectors using Geant4 Monte Carlo with light tracking simulation

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