Development of a dual-head mobile DOI-TOF PET system having multi-modality compatibility

Yamakawa, Yoshiyuki; Kobayashi, Tetsuya; Furuta, Masafumi; Sato, Masanobu; Ohi, Junichi; Tonami, Hiromichi; Furumiya, Tetsuo; Tsuda, Tomoaki; Nakazawa, Masayuki; Hashizume, Nobuya; Kitamura, Kazuhiro

doi:10.1109/nssmic.2014.7430879

Cited by 4 publications

(3 citation statements)

References 7 publications

(3 reference statements)

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“…There are a plethora of applications for MRI in cardiac disease and the opportunity space for multi-modality imaging is large (Nekolla et al 2009). An opportunity for this approach is presented by the portable PET scanner reported by Yoshiyuki et al (2014).…”

Section: Complementary Imagingmentioning

confidence: 99%

Application-specific nuclear medical in vivo imaging devices

Chaudhari¹,

Badawi²

2021

Phys. Med. Biol.

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Nuclear medical imaging devices, such as those enabling photon emission imaging (gamma camera, single photon emission computed tomography, or positron emission imaging), that are typically used in today’s clinics are optimized for assessing large portions of the human body, and are classified as whole-body imaging systems. These systems have known limitations for organ imaging, therefore application-specific devices have been designed, constructed and evaluated. These devices, given their compact nature and superior technical characteristics, such as their higher detection sensitivity and spatial resolution for organ imaging compared to whole-body imaging systems, have shown promise for niche applications. Several of these devices have further been integrated with complementary anatomical imaging devices. The objectives of this review article are to (1) provide an overview of such application-specific nuclear imaging devices that were developed over the past two decades (in the twenty-first century), with emphasis on brain, cardiac, breast, and prostate imaging; and (2) discuss the rationale, advantages and challenges associated with the translation of these devices for routine clinical imaging. Finally, a perspective on the future prospects for application-specific devices is provided, which is that sustained effort is required both to overcome design limitations which impact their utility (where these exist) and to collect the data required to define their clinical value.

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Section: Complementary Imagingmentioning

confidence: 99%

Application-specific nuclear medical in vivo imaging devices

Chaudhari¹,

Badawi²

2021

Phys. Med. Biol.

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“…Limited-angle TOF-PET systems are being investigated for intraoperative surgical applications [6] and for multi-modal compatible flexible PET imaging to fit existing magnetic resonance imaging (MRI) or computed tomography (CT) [7]. Dual panel detectors are being studied to be used for in-beam PET systems used for monitoring proton or heavy ion therapies [8], [9], [10] and also for positron emission mammography [11], [12], [13].…”

Section: Introductionmentioning

confidence: 99%

Multipanel Limited Angle PET System With 50 ps FWHM Coincidence Time Resolution: A Simulation Study

Razdevsek

Dolenec

Križan

et al. 2022

IEEE Trans. Radiat. Plasma Med. Sci.

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In this simulation study, we evaluate the performance of a limited angular coverage PET system consisting of two/four fast-timing 50 ps FWHM CTR flat-panel detectors made of 5 -20 mm long pixelated LSO crystals. We studied image quality and count rates following the NEMA standard, spatial resolution by imaging a Derenzo phantom and a hot rod, and investigated the sensitivity of different scanner designs. We demonstrated the possible use of such a scanner by imaging a human head and a torso of the XCAT digital phantom. All the designs were compared to the reference scanner, based on Siemens Biograph Vision PET/CT scanner geometry. We show that good CTR can compensate for lower detection efficiency or smaller angular coverage. Good image quality can be obtained with a simple limited-angle PET system without distortions or artefacts. Substantial degradation of the spatial resolution with increased crystal length is observed in the two-panel design due to the parallax error, but not in the four-panel design. The four-panel design simulated with a CTR of 50 ps FWHM is comparable to that of the current state-of-the-art clinical PET/CT scanner. Similar fast-timing limited-angle planar detectors could enable much less expensive total-body or single organ (dynamically selectable) imaging devices.

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“…On the other hand, it exponentially increases the number of pixels and complexity of readout front-end, as well as system development cost. The application-specific integrated circuits (ASICs) are widely designed and applied for readout and translation of SiPM array signals into position, energy, and time values in a single or multiple chips using standard anode and cathode outputs of SiPM (Yoshiyuki et al 2014). However, high cost of ASIC chips in addition to the utilization of the third fast output of the SiPM in the current work prevented us from applying such a general chip design.…”

Section: Introductionmentioning

confidence: 99%

Generic high resolution PET detector block using 12 × 12 SiPM array

Sajedi

Zeraatkar

Taheri

et al. 2018

Biomed. Phys. Eng. Express

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With the advancement of the Silicon Photomultiplier (SiPM) technology, these devices are becoming the mainstream for use in high resolution PET detectors especially where the compatibility with magnetic field is critical. Large-area SiPM arrays are now widely used in high resolution PET detector modules. The challenges are emerged in the readout and timing circuitry by the increase of pixel density in the area. The application-specific integrated circuits (ASICs) are developed to readout arrays with standard anode/ cathode outputs. SiPM detection principle, which produces dark current noise in the inactive pixels, makes the multiplexing techniques more challenging rather than the PMT signals. In this work a new generic PET detector block using SiPM arrays with three outputs (anode, cathode, and fast) is presented which is suitable for applications in small animal, brain, and clinical PET imaging. The block detector accepts a 12×12 array with both standard and fast output signals with an overall detector dimension of 50×50 mm 2 . A new version of the scrambled crosswire readout (SCR) method was implemented to reduce 144 'fast outputs' to 9 tile signals and 144 standard outputs to 16 energy channels. The tile signals are also used to generate time pickoff information for timing resolution. We implemented time-to-digital converter (TDC) in Xilinx's SPARTAN6 field programmable gate array (FPGA) by using the 64-tap delay line. This low cost chip performs all required processes for position, energy, time, and interface architecture. The attached 24×24 LYSO:Ce array with 2×2×10 mm 3 pixels is imaged and pixels are resolved clearly in the room temperature. The measured energy resolution of the detector block after calibration for all crystal pixels is 12.4% at 511 keV. Also, the coincidence resolving time for two identical modules was measured at 1.85 ns.

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Development of a dual-head mobile DOI-TOF PET system having multi-modality compatibility

Cited by 4 publications

References 7 publications

Application-specific nuclear medical in vivo imaging devices

Application-specific nuclear medical in vivo imaging devices

Multipanel Limited Angle PET System With 50 ps FWHM Coincidence Time Resolution: A Simulation Study

Generic high resolution PET detector block using 12 × 12 SiPM array

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