Siemens Medical Solutions Usa, Inc.

Other

Siemens Aktiengesellschaft

Siemens Healthineers Ag

Sanghee Cho

Robert A Mintzer

Nan Zhang

Johannes Breuer

James Luke Corbeil

Mehmet Aykac

Peter Hansen

James Christopher Arnott

Maciej P Kapusta

Ralf Ladebeck

Matthias J Schmand

Debora Henseler

Ronald Grazioso

Philipp Hoecht

Martin Judenhofer

Ludwig Eberler

A method is for determining a heating effect of an imaging sequence of a second imaging modality on a detector of a first modality of a combined imaging device in dependence of a reference imaging sequence of the second imaging modality. A further method is for compensating a heating effect of an imaging sequence of a second imaging modality on a detector of a first modality of a combined imaging device. Furthermore, a combined imaging device includes a magnetic resonance imaging device and a first modality including a detector and a temperature compensation unit configured to compensate for a temperature variation of the detector. The combined imaging device is configured to perform a method for determining a heating effect of an imaging sequence of the magnetic resonance imaging device on the detector of the first modality in dependence of a reference imaging sequence of the magnetic resonance imaging device.

Determining a heating effect of a MRI sequence on a diagnostic modality due to the temperature variations and method of predicting and compensating the variations

A scintillation block detector employs an array of optically air coupled scintillation pixels, the array being wrapped in reflector material and optically coupled to an array of silicon photomultiplier light sensors with common-cathode signal timing pickoff and individual anode signal position and energy determination. The design features afford an optimized combination of photopeak energy event sensitivity and timing, while reducing electronic circuit complexity and power requirements, and easing necessary fabrication methods. Four of these small blocks, or 'miniblocks,' can be combined as optically and electrically separated quadrants of a larger single detector in order to recover detection efficiency that would otherwise be lost due to scattering between them. Events are validated for total energy by summing the contributions from the four quadrants, while the trigger is generated from either the timing signal of the quadrant with the highest energy deposition, the first timing signal derived from the four quadrant time-pickoff signals, or a statistically optimum combination of the individual quadrant event times, so as to maintain good timing for scatter events. This further reduces the number of electronic channels required per unit detector area while avoiding the timing degradation characteristic of excessively large SiPM arrays.

Silicon photomultiplier based TOF-PET detector

Systems and methods for configuring a radiation detector are provided. A first event is detected at a first scintillator crystal of a first detector unit. A second coincident event is detected at a second scintillator crystal of a second detector unit adjacent to the first detector unit. Operating parameters are calculated for the first detector unit based on the coincident events.

Setup of SIPM based PET detector using LSO background radiation

A system and method are provided for determining the onset of gamma interactions for positron emission tomography (PET) imaging more accurately than with existing techniques. The timing of a sequence of primary trigger events is obtained and used to determine a weighted combination, which mixes the timing information from the various primary trigger events to compute an overall event trigger timing with improved time resolution. Numerical simulations demonstrate that the invention improves time resolution by approximately 10% over state-of-the-art methods. This improved time resolution directly benefits the imaging performance of the PET scanner, especially in time-of-flight (TOF) mode, where a high time resolution directly translates to a reduction in image noise at the same dose&#x2014;or, alternatively, a reduction of dose to the patient or scan time for the same image quality.

System and method for improving detection of gamma interactions in a positron emission tomography system

A method of configuring a time-of-flight positron emission tomography (PET) system includes determining a set of parameters of a detector of the PET system. Each parameter is configured to affect photon travel within the detector. The method further includes simulating operation of the detector to generate a photon detection timing data profile for a plurality of depth of interaction (DOI) positions within the detector via a simulation model of the detector configured in accordance with the set of parameters, and determining a time-of-flight correction factor for each DOI position of the plurality of DOI positions based on the simulated operation. The correction factor is indicative of a time offset of the photon detection timing data profile.

Optical simulation-based time-of-flight compensation and PET system configuration

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Knoxville, TN, United States of America

Sanghee Cho