Our goal is development of an innovative brain-PET with effective sensitivity (8X) and higher spatial resolution vs. current advanced brain-PET systems by implementation of advanced ultrafast SiPM/readout systems coupled to thin monolithic crystals arranged in “onion ring” geometry with small air-gaps between the rings enabling accurate tracking of Compton Scatter (CS) events followed by photoelectric absorption (PE) events, forming “triplets” (PE =CS-PE). We performed Monte Carlo simulations of four concentric rings with diameters 250, 270, 290, 310 mm, and 508 mm axial length with monolithic 3-mm-thick LYSO thin-slab detector modules. The brain was simulated by a water sphere containing F-18. We considered only true-coincidence (PE=PE) and triplet (PE =CS-PE) events. For triplets, back-to-forward scatter ratio is 0.26. The triplet-to-true-coincidence events ratio is 0.30. Inclusion of triplets in addition to true-coincidence events allows sensitivity increase by ~30%. Because the point-of-first interaction is well defined, the improved spatial resolution is anticipated.
In this study, we re-evaluated the attainable coincidence time resolution (CTR) performance for 3×3×3 mm3 LYSO crystals coupled to matched 3×3 mm2 SiPMs. This work was motivated by potential increased sensitivity in brain positron emission tomography (PET) detector blocks that would be enabled with ultrashort CTR (<100 ps). The recent progress in silicon photomultiplier (SiPM) technology, high-frequency read-out circuits, and optimized data processing is expected to lead directly to improved performance. The 3×3×3 mm3 LYSO crystals, with all sides polished to optical quality, were optically coupled to SiPMs designed and fabricated by Fondazione Bruno Kessler (FBK). An improved high frequency read-out circuit was designed and fabricated. CTR was measured using a 22Na positron source (<10 μCi) sandwiched between two identical LYSO/SiPM/read-out circuit stacks. Our studies show that a CTR of less than 80 ps, which, to the best of our knowledge, is the shortest reported CTR for 3×3×3 mm3 LYSO crystals. The results demonstrate, for the first time, that CTR performance in 3×3×3 mm3 LYSO crystals coupled to a 3mm×3mm2 SiPMs is comparable to CTRs achieved for ultra-small LYSO crystals (2×2×3 mm3) coupled to large 4 × 4 mm2 SiPMs. These results prove that an array of 3×3×3 mm3 LYSO/SiPM can be used to build a next generation high performance detector block with very high packing fraction, enabling ultimately very high gamma ray detection efficiency and very high system sensitivity.
There is a need to lower mass of scintillators in PET imagers. However, the tradeoff between scintillator thickness and axial field of view is not obvious, particularly if the total mass of the scintillator is a limitation. In this work, we developed fast analytical methods to assess performance of PET as a function of scintillator thickness. Calculation of the photopeak detection efficiency (PDE) is complicated by the fact that most incident 511 keV gamma rays first undergo Compton scattering in the scintillator resulting in a partial deposition of energy, as well as the production of a lower energy secondary gamma ray. The PDE is dependent on scintillator geometry and source position and must be recalculated when either changes. We compare Monte Carlo and our analytical lower and upper bound estimation of PDE for thin slab LSO scintillators as a function of its thickness assuming normal incidence. We show that that our analytical method achieves excellent agreement with the results obtained by time-consuming Monte Carlo approach. This is important because application of our fast method enables preliminary system optimization prior to time-consuming, complex Monte Carlo modeling.
Scintigraphy is a common nuclear medicine method to image molecular target’s bio-distribution and pharmacokinetics through the use of radiotracers and gamma cameras. The patient’s images are obtained by using a pair of opposing large flat gamma ray detectors equipped with parallel-hole lead or tungsten collimators that preferentially detect gamma-rays that are emitted perpendicular to the plane of the detector. The resulting images form an anterior/posterior (A/P) planar image pairs. The obtained images are contaminated by noise and contain artifacts caused by gamma-ray attenuation, collimator penetration, scatter and other detrimental factors. Post-filtering of the images can reduce the noise, but at the cost of spatial resolution loss, and cannot remove any of the aforementioned artifacts. In this study, we introduced a new image reconstruction-based method to recover a single corrected planar scintigraphic patient image corrected for attenuation, system spatial resolution and collimator penetration, using the A/P image pair (two conjugated views) as data. To accomplish this task, we used a system model based on the gamma camera detectors physical properties and applied regularization method based on sparse image representation to control noise while preserving spatial resolution. In this proof-of-concept study, we evaluated the proposed approach using simple numerical phantoms. The images were evaluated for simulated lesions images contrast and background variability. Our initial results indicate that the proposed method outperforms the conventional methods. We conclude, that the proposed approach is a promising methodology for improved planar scintigraphic image quality and warrants further exploration.
Most positron emission tomography (PET) systems use an (almost) cylindrically symmetric detector geometry that acquires data in step-wise or continuous fashion. The National Electrical Manufacturers Association (NEMA) has developed performance standards (NEMA NU2-2018) to evaluate the performance of these systems. However, many Brain PET scanners no longer use a cylindrically symmetric detector arrangement; instead favoring unconventional, asymmetric spatial distributions of detectors to improve the geometric efficiency. The comparison of these systems with cylindrical devices is difficult because the NEMA standards may not be directly compatible with these non-cylindrical detector geometries. The incompatibility is due to both the source geometry and use of single-slice-rebinning (SSR). In this study, we extended the standard cylindrical polyethylene phantom used for the noise equivalent count rate (NECR) and scatter fraction (SF) measurements in NEMA NU2-2018 by adding a 20 cm diameter polyethylene sphere with a line-source channel. To avoid the use of SSR in NECR, SF and sensitivity tests, which can incorrectly assign slice locations in non-cylindrical tomographs, we instead propose a different method that uses the known positions of the line-source and the detection points of the line-of-response (LOR). Axial position can be determined from the minimum of the distance between the LOR and the line-source. These correctly binned counts were compared to cylindrical and spherical cap PET geometries using the well-validated GATE Monte Carlo code to estimate performance. The results show that our proposed modifications provide a means to estimate a non-cylindrical tomograph’s NECR, SF,and sensitivity that is consistent with the NEMA methodology.
Developing PET reconstruction algorithms with improved low-count capabilities may provide a timely and cost- effective means of reducing radiation dose in promising clinical applications such as immuno-PET that require long-lived radiotracers. For many PET clinics, the reconstruction protocol consists of postsmoothed ordered-sets expectation-maximization (OSEM) reconstruction, but penalized likelihood methods based on total-variation (TV) regularization could substantially reduce dose. We performed a task-based comparison of postsmoothed OSEM and higher-order TV (HOTV) reconstructions using simulated images of a contrast-detail phantom. An anthropomorphic visual-search model observer read the images in a location-known receiver operating characteristic (ROC) format. Acquisition counts, target uptake, and target size were study variables, and the OSEM postfiltering was task-optimized based on count level. A psychometric analysis of observer performance for the selected task found that the HOTV algorithm allowed a two-fold reduction in dose compared to the optimized OSEM algorithm.
A new challenge for time-of-flight (TOF) Positron Emission Tomography (PET) is achieving 10 ps Coincidence Timing Resolution (CTR). Such a short CTR would enable a 20-fold higher TOF-related effective sensitivity gain (TOF-gain) and direct reconstruction in PET imaging. Ultrashort CTR greatly benefits brain PET imaging because owing to the relatively small size of human head, TOF-gain only begins to be significant for CTR < 150 ps. The Brain PET (BET) consortium evaluates the potential for achieving 10 ps CTR using an updated Monte Carlo modeling program (MCPET3). This new version includes the ability to set a constant refractive index at each scintillator segment face to model the effects of optical index coupling glues. In addition, the new version provides a simple method for evaluating the effect of Cherenkov photons on the CTR. The latest modeling results are compared to recent world-record experimental CTR with good agreement and only a few adjustable parameters. The results indicate that 50 ps CTR is likely to be attained in the near future, but achieving 10 ps CTR will require a number of substantial improvements in PET detector blocks technology. Based on our simulations, we estimate that in order to achieve the 10 ps CTR a 20-fold increase in scintillator intensity (photons/ps) is required, along with additional improvements in single photon timing resolution.
Purpose: Time-of-flight (TOF) been successfully implemented in whole body PET, significantly improving clinical performance. However, for dedicated brain PET systems, TOF has not been a priority due the relatively small size of the human head, where coincidence timing resolution (CTR) below 200 ps is necessary to arrive at substantial performance improvements. The Brain PET (BET) consortium is developing a dual-ended PET detector block concept with ultrafast CTR, high sensitivity and high spatial resolution (X, Y, depth-of-interaction, DOI) that provides a pathway to significantly improved brain PET. Methods: We have implemented analytical and Monte Carlo models of scintillation photons transport in scintillator segments with arbitrary trans-axial cross-section dimensions. Results: Timing performance is independent of trans-axial cross-section as long as there is a gap between the scintillator and reflector wrapping. Intimate contact between the wrapping with the scintillator decreases the percentage of total internally reflected photons, degrading CTR performance. Excellent CTR performance can be achieved using simple fixed voltage thresholding techniques to determine the arrival times at the top and bottom SiPM. The average of the top and bottom arrival time corresponds to the time of gamma ray absorption, while the difference in arrival time corresponds to DOI. A simple algorithm to use the difference in arrival time to compensate for gamma ray transit time and optical photon transit achieves performance within 20% of the Cramer-Rao lower bound. We established that the advanced silicon photomultiplier designs with high single photon detection efficiency (QE=80%) and high single photon timing resolution (SPTR) ~50 ps are critical for achieving ultrafast TOF-PET performance with CTR ~50 ps and ~4 mm DOI resolution.
Purpose: Time-of-flight (TOF) been successfully implemented in whole body PET, significantly improving clinical performance. However, TOF has not been a priority in development of dedicated brain PET systems due the relatively small size of the human head, where coincidence timing resolution (CTR) below 200 ps is necessary to arrive at substantial performance improvements. The Brain PET (BET) consortium is developing a PET detector block with ultrafast CTR, high sensitivity and high spatial resolution (X, Y, depth of interaction, DOI) that provides a pathway to significantly improved brain PET. Methods: We have implemented analytical and Monte Carlo models of scintillation photons transport in scintillator segments with the trans-axial cross-section equal or smaller than 3x3 mm2 . Results: The signal amplitude and timing of W mm x W mm x L mm scintillators (1 mm<W<3 mm, 5 mm <L< 30 mm) are strongly influenced by sidewall surface polish and external reflector. Highly polished surfaces provide nearly perfect total internal reflection (TIR), enabling the ultrafast timing performance to be relatively independent of scintillator crosssection. The signal amplitude in such a configuration does not depend on DOI. However, the differential signal from top and bottom SiPM in the dual-ended readout can be used to determine DOI. Using TIR alone, the average of the photon detection times at the top and bottom SiPMs provides a good estimation of the gamma ray absorption time. Averaging ~10 photons starting from 3rd photon produces the shortest CTR for SPTR=50 ps. Conclusions: We established that the advanced silicon photomultiplier designs with high single photon detection efficiency (QE=60%) and high single photon timing resolution (SPTR =50 ps) are critical for achieving ultrafast TOF-PET performance with CTR ~50 ps and ~4 mm DOI resolution.
Using analytical and Monte Carlo modeling, we explored performance of a lightweight wearable helmet-shaped brain positron emission tomography (PET), or BET camera, based on thin-film digital Geiger avalanche photodiode arrays with Lutetium-yttrium oxyorthosilicate (LYSO) or LaBr3 scintillators for imaging in vivo human brain function of freely moving and acting subjects. We investigated a spherical cap BET and cylindrical brain PET (CYL) geometries with 250-mm diameter. We also considered a clinical whole-body (WB) LYSO PET/CT scanner. The simulated energy resolutions were 10.8% (LYSO) and 3.3% (LaBr3), and the coincidence window was set at 2 ns. The brain was simulated as a water sphere of uniform F-18 activity with a radius of 100 mm. We found that BET achieved >40% better noise equivalent count (NEC) performance relative to the CYL and >800% than WB. For 10-mm-thick LaBr3 equivalent mass systems, LYSO (7-mm thick) had ∼40% higher NEC than LaBr3. We found that 1×1×3 mm scintillator crystals achieved ∼1.1 mm full-width-half-maximum spatial resolution without parallax errors. Additionally, our simulations showed that LYSO generally outperformed LaBr3 for NEC unless the timing resolution for LaBr3 was considerably smaller than that presently used for LYSO, i.e., well below 300 ps.
Purpose: To explore, by means of analytical and Monte Carlo modeling, performance of a novel lightweight and low-cost wearable helmet-shaped Brain PET (BET) camera based on thin-film digital Geiger Avalanche Photo Diode (dGAPD) with LSO and LaBr3 scintillators for imaging in vivo human brain processes for freely moving and acting subjects responding to various stimuli in any environment.
Methods: We performed analytical and Monte Carlo modeling PET performance of a spherical cap BET device and cylindrical brain PET (CYL) device, both with 25 cm diameter and the same total mass of LSO scintillator. Total mass of LSO in both the BET and CYL systems is about 32 kg for a 25 mm thick scintillator, and 13 kg for 10 mm thick scintillator (assuming an LSO density of 7.3 g/ml). We also investigated a similar system using an LaBr3 scintillator corresponding to 22 kg and 9 kg for the 25 mm and 10 mm thick systems (assuming an LaBr3 density of 5.08 g/ml). In addition, we considered a clinical whole body (WB) LSO PET/CT scanner with 82 cm ring diameter and 15.8 cm axial length to represent a reference system. BET consisted of distributed Autonomous Detector Arrays (ADAs) integrated into Intelligent Autonomous Detector Blocks (IADBs). The ADA comprised of an array of small LYSO scintillator volumes (voxels with base a×a: 1.0 ≤ a ≤ 2.0 mm and length c: 3.0 ≤ c ≤ 6.0 mm) with 5–65 μm thick reflective layers on its five sides and sixth side optically coupled to the matching array of dGAPDs and processing electronics with total thickness of 50 μm. Simulated energy resolution was 10.8% and 3.3% for LSO and LaBr3 respectively and the coincidence window was set at 2 ns. The brain was simulated as a sphere of uniform F-18 activity with diameter of 10 cm embedded in a center of water sphere with diameter of 10 cm.
Results: Analytical and Monte Carlo models showed similar results for lower energy window values (458 keV versus 445 keV for LSO, and 492 keV versus 485 keV for LaBr3), and for the relative performance of system sensitivity. Monte Carlo results further showed that the BET geometry had >50% better noise equivalent count (NEC) performance relative to the CYL geometry, and >1100% better performance than a WB geometry for 25 mm thick LSO and LaBr3. For 10 mm thick LaBr3 equivalent mass systems LSO (7 mm thick) performed ~40% higher NEC than LaBr3. Analytic and Monte Carlo simulations also showed that 1×1×3 mm scintillator crystals can achieve ~1.2 mm FWHM spatial resolution.
Conclusions: This study shows that a spherical cap brain PET system can provide improved NEC while preserving spatial resolution when compared to an equivalent dedicated cylindrical PET brain camera and shows greatly improved PET performance relative to a conventional whole body PET/CT. In addition, our simulations show that LSO will generally outperform LaBr3 for NEC unless the timing resolution for LaBr3 is considerably smaller than presently used for LSO, i.e. well below 300 ps.
Wavelet transforms have been successfully applied in many fields of image processing. Yet, to our knowledge, they have never been directly incorporated to the objective function in Emission Computed Tomography (ECT) image reconstruction. Our aim has been to investigate if the ℓ1-norm of non-decimated discrete cosine transform (DCT) coefficients of the estimated radiotracer distribution could be effectively used as the regularization term for the penalized-likelihood (PL) reconstruction, where a regularizer is used to enforce the image smoothness in the reconstruction. In this study, the ℓ1-norm of 2D DCT wavelet decomposition was used as a regularization term. The Preconditioned Alternating Projection Algorithm (PAPA), which we proposed in earlier work to solve penalized likelihood (PL) reconstruction with non-differentiable regularizers, was used to solve this optimization problem. The DCT wavelet decompositions were performed on the transaxial reconstructed images. We reconstructed Monte Carlo simulated SPECT data obtained for a numerical phantom with Gaussian blobs as hot lesions and with a warm random lumpy background. Reconstructed images using the proposed method exhibited better noise suppression and improved lesion conspicuity, compared with images reconstructed using expectation maximization (EM) algorithm with Gaussian post filter (GPF). Also, the mean square error (MSE) was smaller, compared with EM-GPF. A critical and challenging aspect of this method was selection of optimal parameters. In summary, our numerical experiments demonstrated that the ℓ1-norm of discrete cosine transform (DCT) wavelet frame transform DCT regularizer shows promise for SPECT image reconstruction using PAPA method.
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