Siemens Medical Solutions Usa, Inc.

Siemens Aktiengesellschaft

University of Tennessee Research Foundation

Siemens Healthcare Gmbh

Lawrence Livermore National Security, LLC

Cti Pet Systems, Inc.

Siemens Molecular Imaging, Inc.

Matthias J Schmand

Nan Zhang

Mark S Andreaco

Peter Carl Cohen

James Luke Corbeil

Niraj K Doshi

Ronald Nutt

Ronald Grazioso

Lars Aldon Eriksson

Debora Henseler

Mehmet Aykac

A Andrew Carey

Ralf Ladebeck

Ziad Burbar

Charles L Melcher

Robert A Mintzer

Merry A Koschan

Markus Vester

Wolfgang Renz

Hubertus Fischer

Volker Matschl

Piotr Szupryczynski

Alexander Andrew Carey

Charles W Williams

Johannes Breuer

Robert E Nutt

Bernd J Pichler

Mohit Tyagi

Günter Schnur

Harry Hedler

Ralph Oppelt

Michael E Casey

Stephen Anthony Payne

Vladimir Y Panin

Nerine Jane Cherepy

Klaus Huber

Sven Zuehlsdorff

Christian J Michel

Troy Marlar

Paul Schleyer

Zachary M Seeley

Brant Quinton

Bruce S Spottiswoode

Dongming Hu

Sanghee Cho

Rainer Paul

Maciej P Kapusta

Ron Grazioso

Michael D Loope

Matthew Eric Martin

Charles H Hayden, Jr

Gregory J Hayzen

Marcus Vester

Christof Thalhammer

Sridhar Kuppuswamy

Guenter Schnur

A PET system for a PET/MRI machine is disclosed. The PET system includes a PET detector assembly arranged to form a single gap aligned with the high-density support structure assembly and the shielded cable assembly that run along the patient bed in the PET/MRI machine. The PET detector arrangement maximizes the allowable diameter of the PET system within the MR magnet and ensures that the high-density material does not interfere with image acquisition. Further, various image reconstruction techniques compatible with the PET detector arrangement are described.

Arrangement of pet detectors for combined PET/MR systems

Systems and methods of PET attenuation correction using low-field MR image data includes receiving a first set of image data and a set of low-field magnetic resonance (MR) image data. An attenuation correction map is generated from the low-field MR image data using a first trained neural network. At least one attenuation correction process is applied to the first set of image data based on the attenuation correction map to generate at least one clinical attenuation-corrected image.

Systems and methods for low field MR/PET imaging

The present disclosure discloses, in one arrangement, a scintillator material made of a metal halide with one or more additional group-13 elements. An example of such a compound is Ce:LaBrwith thallium (Tl) added, either as a codopant or in a stoichiometric admixture and/or solid solution between LaBrand TlBr. In another arrangement, the above single crystalline iodide scintillator material can be made by first synthesizing a compound of the above composition and then forming a single crystal from the synthesized compound by, for example, the Vertical Gradient Freeze method. Applications of the scintillator materials include radiation detectors and their use in medical and security imaging.

Metal halide scintillators with reduced hygroscopicity and method of making the same

The present disclosure discloses rare earth metal halide scintillators compositions with reduced hygroscopicity. Compositions in specific implementations include three group of elements: Lanthanides, (La, Ce, Lu, Gd or V), elements in group 17 of the periodic table of elements (CI, Br and I) and elements of group 13 (B, AI, Ga, In, TI), and any combination of these elements. Examples of methods for making the compositions are also disclosed.

Rare-earth metal halide scintillators with reduced hygroscopicity and method of making the same

Example embodiments of a radiation detection system including a detector is described. The detector can include a scintillator, a sensor, and a light source. The radiation detection system can further include a controller programmed to control the light source to expose the scintillator to a light to saturate traps in the scintillator. In some embodiments, the detector can further include a second light source, and the controller is programmed to control the second light source to expose the scintillator to a second light to detrap afterglow traps in the scintillator.

Radiation detector for imaging applications with stabilized light output

A detector, includes a plurality of photomultiplier tubes each having an anode configured to generate an anode output signal and a frequency domain detector interface including a plurality of frequency domain coupling circuits. Each of the plurality of frequency domain coupling circuits is configured to receive the anode output signal from one of the plurality of photomultiplier tubes and pickoff one of a high-frequency component or a low-frequency component. Each of the plurality of frequency domain coupling circuits is further configured to generate a pass-through signal comprising a first of the high-frequency component or the low-frequency component.

Analog frequency-domain multiplexing for time-of-flight pet detector frontend electronics

A radiation detector comprises a first scintillator having a first peak wavelength and a second scintillator positioned on the first scintillator. The second scintillator has a second peak wavelength different from the first peak wavelength. A plurality of photon detectors are provided. The first scintillator is positioned over and contacts each of the plurality of photon detectors. The plurality of photon detectors include first detectors and second detectors. The second detectors differ from the first detectors in doping profile, pn junction depth, or front-versus-backside illumination geometry. The first detectors are more sensitive to the first peak wavelength than the second peak wavelength. The second detectors are more sensitive to the second peak wavelength than the first detectors.

Radiation detector capable of measuring depth-of-interaction

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 detector system for time-of-flight (TOF) positron emission topography (PET) includes an analog silicon photomultiplier (aSiPM) configured to detect at least one photon event. The aSiPM has an anode and a cathode. A transformer has a first side electrically coupled to the aSiPM to form a low-impedance current loop between the anode and the cathode of the transformer. An impedance ratio of the transformer N reduces an effective terminal resistance of the aSiPM. An amplifier is electrically coupled to a second side of the transformer. The amplifier has negative feedback path configured to minimize the voltage swing between a non-inverting input and an inverting input. The negative feedback path reduces an effective terminal capacitance and an effective load impedance of the aSiPM.

Bootstrapping readout for large terminal capacitance analog-SiPM based time-of-flight PET detector

APD-based PET modules are provided for use in combined PET/MR imaging. Each module includes a number of independent, optically isolated detectors. Each detector includes an array of scintillator (e.g. LSO) crystals read out by an array of APDs. The modules are positioned in the tunnel of a MR scanner. Simultaneous, artifact-free images can be acquired with the APD-based PET and MR system resulting in a high-resolution and cost-effective integrated PET/MR system.

Combined PET/MR imaging system and APD-based PET detector for use in simultaneous PET/MR imaging

In one embodiment, a method includes forming a powder having a composition with the formula: ABCO, where h is 3&#xb1;10%, i is 2&#xb1;10%, j is 3&#xb1;10%, A includes one or more rare earth elements, B includes aluminum and/or gallium, and C includes aluminum and/or gallium. The method additionally includes consolidating the powder to form an optically transparent ceramic, and applying at least one thermodynamic process condition during the consolidating to reduce oxygen and/or thermodynamically reversible defects in the ceramic. In another embodiment, a scintillator includes (GdY)(GaAl)OD, where a is from about 0.05-2, b is from about 1-3, x is from about 2.8-3.2, y is from about 4.8-5.2, c is from about 0.003-0.3, and D is a dopant, and where the scintillator is an optically transparent ceramic scintillator having physical characteristics of being formed from a ceramic powder consolidated in oxidizing atmospheres.

Transparent ceramic garnet scintillator detector for positron emission tomography

A nuclear imaging system includes a detector configured to detect at least one photon event. A timing signal path is electrically coupled to the detector. The timing signal path is configured to generate a timing signal indicative of a timing of the at least one photon event. An energy signal path is also electrically coupled to the detector. The energy signal path is configured to generate an energy signal indicative of an energy of the at least one photon event. A time-domain multiplexer is configured combine the timing signal and the energy signal into a compound signal.

Transmission of PET-signals by means of time division multiplexing

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

A radiation detector may include a scintillator, a light source, and a sensor. The scintillator may include various scintillation materials capable of converting non-visible radiation (incoming radiation) into visible light. The sensor may be placed in adjacent or in close proximity to the scintillator, such that any converted visible light may be detected or measured by the sensor. The light source may be placed in adjacent or in close proximity to the scintillator, such that light from the light source may interact with defects in the scintillator to minimize interference on the conversion of non-visible radiation into visible light caused by the defects.

Growing community of inventors

Lenoir City, TN, United States of America

Matthias J Schmand