Siemens Medical Solutions Usa, Inc.

Other

The University of Tennessee Research Foundation

Siemens Healthineers Ag

Robert A Mintzer

Sanghee Cho

Johannes Breuer

Mark S Andreaco

Matthias J Schmand

James Luke Corbeil

Nan Zhang

Peter Carl Cohen

Stefan B Siegel

Mehmet Aykac

Peter Hansen

James Christopher Arnott

Maciej P Kapusta

Derek W Austin

Harry Hedler

Ralf Ladebeck

Charles L Melcher

Merry A Koschan

Alexander Andrew Carey

Philipp Hoecht

Aaron McFarland

Mu Chen

Danny F Newport

Martin Judenhofer

Anne M Smith

Bing Feng

Christof Thalhammer

Casey Barrett Holbrook

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

Disclosed herein is a scintillator comprising a plurality of garnet compositions in a single block having the structural formula (1):MMMMO&#x2003;&#x2003;(1)where O represents oxygen, M, M, M, and Mrepresents a first, second, third and fourth metal that are different from each other, where the sum of a+b+c+d is about 8, where 'a' has a value of 2 to 3.5, 'b' has a value of 0 to 5, &#x201c;c&#x201d; has a value of 0 to 5 &#x201c;d&#x201d; has a value of 0 to 1, where &#x201c;b&#x201d; and &#x201c;c&#x201d;, &#x201c;b&#x201d; and &#x201c;d&#x201d; or &#x201c;c&#x201d; and &#x201c;d&#x201d; cannot both be equal to zero simultaneously, where Mis rare earth element including gadolinium, yttrium, lutetium, or a combination thereof, Mis aluminum or boron, Mis gallium and Mis a codopant; wherein two compositions having identical structural formulas are not adjacent to each other and wherein the single block is devoid of optical interfaces between different compositions.

Ceramic phoswich with fused optical elements, method of manufacture thereof and articles comprising the same

A scintillator element is disclosed where the scintillator element includes a scintillator formed of a scintillation material capable of converting non-visible radiation into scintillation light, wherein the scintillator has a plurality of laser-etched micro-voids within the scintillator, each micro-void having an interior surface, and an intrinsic reflective layer is formed on the interior surface of at least some of the micro-voids, wherein the intrinsic reflective layer is formed from the scintillation material.

Laser etched scintillation detector blocks with internally created reflectors

Disclosed herein is a method including disposing in a mold a powder that has a composition for manufacturing a scintillator material and compressing the powder to form the scintillator material; where an exit surface of the scintillator material has a texture that comprises a plurality of projections that reduce total internal reflection at the exit surface and that increase the amount of photons exiting the exit surface by an amount of greater than or equal to 5% over a surface that does not have the projections.

Method of manufacturing garnet interfaces and articles containing the garnets obtained therefrom

A method () of operation of a PET scanner () that determines the depth of interaction of the annihilation photons within the scintillator () in localizing a temporal photon pair along a line of response (LOR).

Depth-of-interaction in an imaging device

A system and method for reconstructing single photon emission computed tomography data acquired with a pinhole collimator includes sub-dividing each voxel in the imaging target object space into sub-voxels and sub-dividing each of the detector bins in the gamma camera detector into sub-bins, connecting the centers of each of the sub-voxels to each of the detector sub-bins through a pinhole provided in the pinhole collimator by ray tracing and for each ray connecting the centers of each of the sub-voxels to each of the detector sub-bins, the transmission probability is calculated by analytically solving the intersections between the ray and the pinhole surfaces. Then, a geometric-response-function of the pinhole collimator is computed which is then convolved with the intrinsic-response-function of the detector to obtain the PSF.

Modeling of the point-spread-function in single-pinhole and multi-pinhole spect reconstruction

A method for processing events in a medical imaging device may comprise the steps of receiving analog signals from at least one PMT into an Applied Specific Integrated Circuit (ASIC) comprising a Constant Fraction Discriminator (CFD) and transmitting analog outputs from the ASIC. Further, sampling the analog outputs continuously using an Analog to Digital Converter (ADC) and transmitting digital outputs; and collecting a number of samples of the digital output during a sampling period using a Field Programmable Gate Array (FPGA) when triggered by the CFD. The method may additionally determine the energy of the analog signals from the at lease one PMT by subtracting the peak value of each signal from the baseline value of each signal, wherein the peak value is determined as an average of at least one sample taken only around the peak during the sampling period, and the baseline value is determined as an average of at least one sample taken only around the beginning or end of the sampling period.

Method for energy calculation and pileup determination for continuously sampled nuclear pulse processing

A grid suitable for being positioned and held in relation to a detector has positive positioning means and at least one magnet for holding the grid.

Magnetically retained interchangeable collimators for scintillation cameras

Growing community of inventors

Knoxville, TN, United States of America

Robert A Mintzer