Torsten Solf

Temporal artifacts in flat dynamic x-ray detectors

Flat X-ray detectors based on CsI:Tl scintillators and amorphous silicon photodiodes are known to exhibit temporal artefacts (ghost images) which decay over time. Previously, these temporal artefacts have been attributed mainly to residual signals from the amorphous silicon photodiodes. More detailed experiments presented here show that a second class of effects, the so-called gain effects, also contributes significantly to the observed temporal artefacts. Both the residual signals and the photodiode gain effect have been characterized under various exposure conditions in the study presented here. The results of the experiments quantitatively show the decay of the temporal artefacts. Additionally, the influence of the detectors reset light on both effects in the photodiode has been studied in detail. The data from the measurements is interpreted based on a simple trapping model which suggests a strong link between the photodiode residual signals and the photodiode gain effect. For the residual signal effect a possible correction scheme is described. Furthermore, the relevance of the remaining temporal artefacts for the applications is briefly discussed for both the photodiode residual signals and the photodiode gain effect.

MR compatibility aspects of a silicon photomultiplier-based PET/RF insert with integrated digitisation

The combination of Positron Emission Tomography (PET) and Magnetic Resonance Imaging (MRI) into a single device is being considered a promising tool for molecular imaging as it combines the high sensitivity of PET with the functional and anatomical images of MRI. For highest performance, a scalable, MR compatible detector architecture with a small form factor is needed, targeting at excellent PET signal-to-noise ratios and time-of-flight information. Therefore it is desirable to use silicon photo multipliers and to digitize their signals directly in the detector modules inside the MRI bore. A preclinical PET/RF insert for clinical MRI scanner was built to demonstrate a new architecture and to study the interactions between the two modalities.The disturbance of the MRIs static magnetic field stays below 2 ppm peak-to-peak within a diameter of 56 mm (90 mm using standard automatic volume shimming). MRI SNR is decreased by 14%, RF artefacts (dotted lines) are only visible in sequences with very low SNR. Ghosting artefacts are visible to the eye in about 26% of the EPI images, severe ghosting only in 7.6%. Eddy-current related heating effects during long EPI sequences are noticeable but with low influence of 2% on the coincidences count rate. The time resolution of 2.5 ns, the energy resolution of 29.7% and the volumetric spatial resolution of 1.8 mm(3) in the PET isocentre stay unaffected during MRI operation. Phantom studies show no signs of other artefacts or distortion in both modalities. A living rat was simultaneously imaged after the injection with (18)F-Fluorodeoxyglucose (FDG) proving the in vivo capabilities of the system.

SiPM based preclinical PET/MR insert for a human 3T MR: first imaging experiments

Simultaneous PET/MRI is a hybrid imaging modality which promises to play an important role in the field of molecular imaging, as it combines the outstanding soft-tissue contrast of MRI with the metabolic and functional information of PET and MRI. In addition, the possibility for true simultaneous acquisition allows for improved 4D registration which in due course may lead to enhanced image quality and image quantification. The main technical challenges of simultaneous PET/MR are the MR-based attenuation correction and the development of an MR-compatible PET detector technology. Avalanche photo diode based detectors have been already successfully integrated into preclinical as well as human systems [1,2]. Low but noticeable interferences between PET and MRI have been reported so far. Unfortunately, these implementations do not offer the measurement of time of flight (TOF) information in the sub-ns range, which is one of the drivers for high quality clinical PET and has been state-of-the-art in clinical PET/CT for the last 5 years.

Towards Software-Based Real-Time Singles and Coincidence Processing of Digital PET Detector Raw Data

This paper presents a software-based singles and coincidence processing (SCP) architecture for a digital PET/MR system that is based on SiPM detectors with local digitization coupled to preclinical crystal arrays. Compared with traditional PET systems, our system outputs detector raw data of the individual detector elements via optical Gigabit Ethernet interfaces instead of singles or coincidences. The raw data contains the digitized timestamps, energies, and identifiers of triggered SiPM pixels (hits). Although this approach requires a high bandwidth for the detector data transmission system, the availability of detector raw data offers unique opportunities to employ more accurate and computationally complex, iterative algorithms, which can lead to PET images with higher quality and accuracy. In this paper, we evaluate a parallel software-based SCP for three different crystal position estimation approaches with regard to its real-time capabilities. The SCP receives detector raw data as input and outputs list-mode coincidence data. The investigated PET system features ten singles processing units (SPU), each equipped with two PET detector stacks and a Gigabit Ethernet interface to a data acquisition and processing server (Dell Poweredge R910 equipped with 4× Intel Xeon X7560@2.27 GHz CPUs and 256 GByte DDR3-RAM), allowing lossless real-time acquisition of the entire raw data stream. Using the detector raw data of three previously stored measurements, our results show that the throughput (in Mhits/s) of a center-of-gravity (COG)-based parallel SCP is nearly 4× higher on average than the estimated detector raw data output that is generated from an activity of 37 MBq in the iso-center of the detector ring. Under the same conditions, an iterative maximum-likelihood (ML)-based parallel SCP leads to a 6× higher throughput on average, while a Gaussian-based parallel SCP also results in a 13× higher throughput on average. Compared with a serial processing approach, the parallel implementations show speedups of up to 38× on average for the ML-based, 39× on average for Gaussian-based, and up to 34× on average for the COG-based parallelized SCP for the three previously-stored measurements.

Maximum likelihood based positioning and energy correction for pixelated solid state PET detectors

As part of a preclinical MR compatible small animal PET scanner, a compact block detector for gamma-ray detection has been developed. The block detector consists of a LYSO crystal array with 22 × 22 pixels and an array of 8 × 8 Silicon photomultiplier. An intermediate light guide enables positioning by light-sharing. Due to dark noise and variations of the photomultiplier gain and the light collection efficiency, the crystal identification and energy computation using the center of gravity method is erroneous. We propose an alternative positioning scheme that is based on maximizing the likelihood of the scintillation events. The method directly gives the index of the active crystal pixel and allows also to correct the registered gamma-ray energy. First studies show that the all-over energy resolution for one block detector is enhanced from about 28% to 15%. For the used data set, energy correction with the presented method clearly outperforms energy correction based on the center of gravity method.

Solid-state detector stack for ToF-PET/MR

The integration of PET and MR imaging requires a novel type of highly integrated PET detector. To cope with geometric constraints and MR compliance a very compact detector stack was built within the HYPERImage consortium. This allows a four side buttable detector module design with a low dead space in between. The scintillation light coming from a LYSO array is converted in a SiPM sensor tile with a high packing fraction and a high photo detection efficiency to provide sub-ns time-of-flight timing resolution. The analog signals coming from the SiPM elements are digitized close to the sensor to minimize potential crosstalk. A custom mixed-signal ASIC was integrated on a 64 channel sensor stack which is powered and controlled by an FPGA interface board. The complete sensor stack is assembled and characterized to extract the PET relevant parameters, in particular energy, timing and spatial resolution for clinical and pre-clinical PET/MR applicationsB.

Multi-Channel Readout ASIC for ToF-PET

An architecture for the simultaneous measurement of arrival time and amplitude of PET scintillation signals in a multichannel chip has been developed. The design of a first prototype chip is described in this paper. An intrinsic time resolution of 105 ps (FWHM) channel-to-channel has been observed with test pulses. In a PET setup with two LYSO crystals equipped with photomultipliers, the coincidence time resolution is 330 ps (FWHM). An energy resolution of 13% could be obtained for 511 keV signals from a Na-22 source using the on-chip charge integrator.

ToF Performance Evaluation of PET Modules With Digital Silicon Photomultiplier Technology During MR Operation

In 2012, we presented the Hyperion-II D preclinical PET insert which uses Philips Digital Photon Countings digital SiPMs and is designed to be operated in a 3-T MRI. In this work we use the same platform equipped with scintillators having dimensions closer to a clinical application. This allows an investigation of the time of flight (ToF) performance of the platform and its behavior during simultaneous MR operation. We employ LYSO crystal arrays of 4×4 ×10 mm3 coupled to 4 ×4 PDPC DPC 3200-22 sensors (DPC) resulting in a one-to-one coupling of crystals to read-out channels. Six sensor stacks are mounted onto a singles processing unit in a 2 ×3 arrangement. Two modules are mounted horizontally facing each other on a gantry with a crystal-to-crystal spacing of 217.6 mm (gantry position). A second arrangement places the modules at the maximum distance of approximately 410 mm inside the MR bore (maximum distance position) which brings each module close to the gradient system. The DPCs are cooled down to approximately 5-10° C under operation. We disable 20% of the worst cells and use an overvoltage of Vov = 2.0 V and 2.5 V. To obtain the best time stamps, we use the trigger scheme 1 (first photon trigger), a narrow energy window of 511 ±50 keV and a minimum required light fraction of the main pixel of more than 65% to reject intercrystal scatter. By using a 22Na point source in the isocenter of the modules, the coincidence resolution time (CRT) of the two modules is evaluated inside the MRI system without MR activity and while using highly demanding gradient sequences. Inside the B0 field without any MR activity at an overvoltage of Vov = 2.0 V, the energy resolution is 11.45% (FWHM) and the CRT is 250 ps (FWHM). At an overvoltage of Vov = 2.5 V, the energy resolution is 11.15% (FWHM) and the CRT is 240 ps (FWHM). During a heavy z-gradient sequence (EPI factor: 49, gradient strength: 30 mT/m, slew rate: 192.3 mT/m/ms, TE/TR: 12/25 ms and switching duty cycle: 67%) at the gantry position and an overvoltage of Vov = 2.0 V, the energy resolution is degraded relatively by 4.1% and the CRT by 25%. Using the same sequence but at the maximum distance position and an overvoltage of Vov = 2.5 V, we measure a degradation of the energy resolution of 9.2% and a 52% degradation of the CRT. The Hyperion-IID platform proofs to deliver good timing performance and energy resolution inside the MRI system even under highly demanding gradient sequences.

Compact SiPM based detector module for time-of-flight PET/MR

We present a compact detector module for γ detection in the PET part of a simultaneous ToF-PET/MR system. The module covers an area of 3:3 cm × 3:3 cm with 64 SiPM based readout channels. It is composed of a stack of three PCBs of identical size: The SiPMs on the topmost PCB are read out by two full-custom ASICs located on a second PCB located underneath. A third PCB at the bottom of the stack contains a local voltage regulator, an FPGA for ASIC control and data processing, and DACs to generate bias voltages for the readout ASICs and the SiPM devices. An LYSO scintillator block is optically coupled to the SiPMs for gamma to light conversion.

Assessment of photodiodes as a light detector for PET scanners

Current PET systems based on pixelated scintillator arrays coupled to photomultiplier tubes suffer from pile-up and electronics dead time at high count rates. With a pixelated readout, i.e. one-to-one coupling of a scintillator crystal to a photo detector, these effects can be strongly reduced. Recent developments of high light output scintillators like LYSO and LaBr3 in combination with very low noise amplifiers based on modern CMOS processes make it possible to use high quantum efficiency blue-sensitive PIN photodiodes as a light detector. To explore the potential of this approach, a model of the signal detection chain was implemented. It comprises the scintillation light pulse and its quantum noise, optical coupling, charge conversion in the diode, noise sources of the integrating amplifier, shaper circuits for the energy and timing channel, and the discriminator for the timing channel. The model is verified using off-the-shelf PIN photodiodes and a dedicated CMOS preamplifier excited by a picosecond laser as well as scintillator pulses. The model predicts that with high light output scintillators, high quantum efficiency photodiodes and optimized preamplifiers, a pixelated PET readout with very good energy resolution and sufficient timing resolution can be realized. To complement the study, an APD-based readout is also considered and the related signal to noise issues are discussed