Cti Pet Systems, Inc.

Siemens Medical Solutions Usa, Inc.

Other

Cti, Inc.

Computer Technology and Imaging, Inc.

Advanced Biomarker Technologies, LLC

Ortec, Inc.

Ronald Nutt

Michael E Casey

Matthias J Schmand

Charles W Williams

Mark S Andreaco

Mehmet Aykac

Niraj K Doshi

J Clifton Moyers

James Luke Corbeil

William F Jones

Lars Aldon Eriksson

Robert E Nutt

David W Townsend

Wolfgang Renz

Ralf Ladebeck

Nan Zhang

Hubertus Fischer

Charles C Watson

Bernd J Pichler

Günter Schnur

Lynda J Nutt

Terry D Douglass

Markus Vester

Stephen David Miller

Charles L Melcher

James J Hamill

Ronald Grazioso

Troy Marlar

Brant Quinton

Ron Grazioso

Terry D Douglas

Marcus Vester

Kelly Milam

Guenter Schnur

A Time-Resolved PET imaging system for producing an event-by-event, real-time, high resolution, three-dimensional positron emission tomographic images without performing sinogram formation or image reconstruction. The third dimension is provided by measuring the &#x394;T between the arrival times of gamma rays from a positron event being detected by two cooperating detectors. In order to determine the location of a positron event along the lines of response, the measurement includes a fast scintillator, constant fraction discriminator and the digital intervalometer. The arrival time of each photon in the annihilation process is recorded with respect to a clock frequency with picosecond resolution. This approach requires significantly fewer positron events, thus requiring fewer detectors, thereby resulting in an gamma event-by-gamma event, real-time TPET imaging system that is more efficient and more economical to produce than conventional PET systems.

Time-resolved positron emission tomography encoder system for producing event-by-event, real-time, high resolution, three-dimensional positron emission tomographic image without the necessity of performing image reconstruction

A Time-Resolved PET imaging system for producing real-time, high resolution, three-dimensional positron emission tomographic images without performing sinogram formation or image reconstruction. The third dimension is provided by measuring the &#x394;T between the arrival times of gamma rays from a positron event being detected by two cooperating detectors. In order to determine the location of a positron event along the lines of response, the measurement includes a fast scintillator, constant fraction discriminator and the digital intervalometer. The arrival time of each photon in the annihilation process is recorded with respect to a clock frequency with picosecond resolution. This approach requires significantly fewer positron events, thus requiring fewer detectors, thereby resulting in a new, real-time TPET imaging system that is more efficient and more economical to produce than conventional PET systems.

Time-resolved positron emission tomography encoder system for producing real-time, high resolution, three dimensional positron emission tomographic image without the necessity of performing image reconstruction

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

A cantilever device for extending capacity of a scale used in a crystal growth apparatus having a pulling head wherein upward movement of a support column in the pulling head decreases a weight measured by the scale. The device includes a horizontal arm having first and second brackets, wherein the first bracket is attached to the pulling head. The device also includes a plate that extends through openings in the first and second brackets, wherein the plate includes a contact end and a free end. Further, the device includes a flexible element attached between the arm and the plate to form a pivot to enable rotation of the plate. A load is positioned on the plate wherein the load causes rotation of the plate about the pivot to cause upward movement of the contact end to move the support column upward to decrease weight measured by the scale.

Cantilever device for extending capacity of a scale used in a crystal growth apparatus

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

A low-volume biomarker generator for producing ultra-short lived radiopharmaceuticals. The low-volume biomarker generator system includes a low-power cyclotron and a radiochemical synthesis system. The cyclotron of the low-volume biomarker generator is optimized for producing radioisotopes useful in synthesizing radiopharmaceuticals in small quantities down to approximately one (1) unit dose. The cyclotron incorporates permanent magnets in place of electromagnets and/or an improved rf system to reduce the size, power requirements, and weight of the cyclotron. The radiochemical synthesis system of the low-volume biomarker is a small volume system optimized for synthesizing the radiopharmaceutical in small quantities of approximately one (1) unit dose.

Low-volume biomarker generator

A combined PET and X-Ray CT tomograph for acquiring CT and PET images sequentially in a single device, overcoming alignment problems due to internal organ movement, variations in scanner bed profile, and positioning of the patient for the scan. In order to achieve good signal-to-noise (SNR) for imaging any region of the body, an improvement to both the CT-based attenuation correction procedure and the uniformity of the noise structure in the PET emission scan is provided. The PET/CT scanner includes an X-ray CT and two arrays of PET detectors mounted on a single support within the same gantry, and rotate the support to acquire a full projection data set for both imaging modalities. The tomograph acquires functional and anatomical images which are accurately co-registered, without the use of external markers or internal landmarks.

Method for acquiring PET and CT images

A biomarker generator system for producing approximately one (1) unit dose of a biomarker. The biomarker generator system includes a small, low-power particle accelerator ('micro-accelerator') and a radiochemical synthesis subsystem having at least one microreactor and/or microfluidic chip. The micro-accelerator is provided for producing approximately one (1) unit dose of a radioactive substance, such as a substance that emits positrons. The radiochemical synthesis subsystem is provided for receiving the radioactive substance, for receiving at least one reagent, and for synthesizing the approximately one (1) unit dose of a biomarker.

Biomarker generator system

An apparatus for an improved cyclotron for producing radioisotopes especially for use in association with medical imaging. The improved cyclotron is configured without a conventional electromagnetic coil. A plurality of dees and a plurality of permanent magnets are alternately disposed in a circular array, each defining a channel through which ions travel. The vacuum chamber wall defines an opening disposed at the center of the array, the opening being configured to receive an ion source. Positive ions flowing from the ion source are exposed to the magnetic field generated by permanent magnets. The positive ions are repelled as they exit a positively charged dee. Negatively charged dees pull the ions. Each time the particles pass through the gap approaching the dees and as they leave the dee and pass through the magnets, they gain energy, so the orbital radius continuously increases and the particles follow an outwardly spiraling path. The disclosure also includes a system composed of a particle accelerator combined with a microreactor or microfluidic chip to produce molecular imaging biomarkers.

Cyclotron having permanent magnets

A detector array including a plurality of scintillators for use in association with an imaging device. The detector array is provided for accurate determination of the location of the impingement of radiation upon an individual scintillator detector. An air gap is disposed between the scintillator elements, thereby increasing the packing fraction and overall sensitivity of the array. The amount of light transmitted down the scintillator element and the amount of light transmitted to adjacent elements is modified to optimize the identification of each element in a position profile map by adjusting the surface finish of the detector elements.

Detector array utilizing air gaps as a reflector between array elements

Apparatus and method for providing nuclear medical imaging, in particular positron emission tomography, wherein a panel detector including scintillation blocks with a light guide is attached thereto. The scintillation block is arranged to cover a plurality of photosensors in an N by N configuration where there are outer photosensors which share light information from adjacent scintillation blocks and at least one center photosensor which does not share light information from adjacent scintillation blocks.

Photo sensor panel for high resolution PET

A detector for use in imaging applications includes at least one detector array, an array of photodetectors, and a continuous light guide disposed between the detectors and the photodetectors. The light guide is continuous over the entire area of the photodetectors and detectors. The thickness of the light guide is optimized based on the shape of the photodetector array. Each detector array includes a plurality of scintillator elements disposed in an M&#xd7;N array, where 'M' and 'N' are independently selectable and are each at least one. A mechanism for maintaining the relative positions of the individual scintillator elements with respect to each other is provided. The retainer is further provided to enhance the separation between the individual detector arrays to define distinct boundaries between the position profiles of the scintillator arrays.

Detector array using a continuous light guide

A method for fabricating an array adapted to receive a plurality of scintillators for use in association with an imaging device. The method allows the creation of a detector array such that location of the impingement of radiation upon an individual scintillator detector is accurately determinable. The array incorporates an air gap between all the scintillator elements. Certain scintillators may have varying height reflective light partitions to control the amount of light sharing which occurs between elements. Light transmission is additionally optimized by varying the optical transmission properties of the reflective light partition, such as by varying the thickness and optical density of the light partitions. In certain locations, no light partitions exist, thereby defining an air gap between those elements. The air gap allows a large increase in the packing fraction and therefore the overall sensitivity of the array.

Detector array using internalized light sharing and air coupling

Combined PET and X-ray CT tomograph

Combined PET and X-ray CT tomograph and method for using same

Growing community of inventors

Knoxville, TN, United States of America

Ronald Nutt