University of Washington

Koninklijke Philips Corporation N.v.

Zecotek Imaging Systems Pte. Ltd.

Robert S Miyaoka

Thomas K Lewellen

Larry A Pierce, Ii

Lawrence R MacDonald

Scott Hauck

Robert L Harrison

William C J Hunter

Michael Haselman

Lingxiong Shao

Thomas Leroy Laurence

Abdelmounaime Faouzi Zerrouk

David Sowards-Emmerd

Kyle Morgan Champley

Robert Stewart

Thomas Lewellen

William Hunter

Adrienne Lehnert

Hubert Vesselle

Larry A Pierce Ii

Various devices, systems, and methods for performing personalized dosimetry of a patient receiving a radiopharmaceutical are described. In an example method, anatomic data is generated by performing a computed tomography (CT) scan on the patient when they are lying down and wearing a garment. Based on the anatomic data, locations of organs of the patient are determined with respect to one or more fiducial markers integrated with the garment. Detectors for detecting photons from a radiopharmaceutical are placed on the garment based on locations of the organs. Subsequently, the patient may be administered a dose of the radiopharmaceutical. When the patient wears the garment, the detectors may detect photons released from the decaying radiopharmaceutical that is distributed in the organs. The radiation dosage to the organs may be determined based on the detected photons.

Devices, systems, and methods for personalized dosimetry

A garment for detecting radiation washout (e.g., radioactivity concentrations) in organs includes a covering that wraps around and is secured to the body. The covering permits positron emission tomography-computed tomography (PET/CT) imaging of the body through the covering. The garment includes guides formed from a material that is visible in a computed tomography (CT) image of the garment, such that the guides are visible in CT images of user organs that the garment overlies. A plurality of radiation detectors are attached to the covering in a configuration customized for the body. A wiring system connects the plurality of radiation detectors to a power and data control system that is configured to transmit data from the garment to a remote service provider.

Multi-detector personalized home dosimetry garment

Various noncollimated single photon emission computed tomography (SPECT) technologies are described herein. An example device includes an array of detectors configured to detect a flux of first photons transmitted from a field of view (FOV) over time. The device also includes an attenuator disposed between the array of detectors and the FOV. The attenuator is configured to move over time and to attenuate second photons emitted from the source. In various implementations, the attenuator is not a collimator. Based on the fluxes of the first photons detected by the detectors, and the position of the attenuator over time, an imaging system may be configured to generate an image of the FOV.

Noncollimated single-photon emission computed tomography

A method for calibrating a nuclear medicine tomography detector module using principal component analysis is based on the idea that calibration beam data lies on a one-dimensional path within the higher dimensional dataspace of output data. The module includes a weighted multiplexing circuit that generates a small number of multiplexed signals for each photon event. Calibration data for the module is generated and analyzed using several iterations of principal component analyses, to filter scattering events, noise, and other spurious signals. The direction of depth-of-interaction information has been found in the high-dimensional dataspace to be indicated by the primary principal component of the calibration data. The primary principal components, principal components from filtered datasets, intermediate thresholds, and DOI or inner product values are recorded for calibrating the module.

Accurate photon depth-of-interaction decoding and calibration of multiplexed detector modules

A photon detector includes a sensor array of optical sensors disposed in a plane and four substantially identical scintillation crystal bars. Each optical sensor is configured to sense luminescence. Each of the four scintillator crystal bars being a rectangular prism with four side surfaces and first and second end surfaces, each scintillation bar has two side surfaces which each face a side surface of another scintillation bar, and each scintillation crystal bar generating a light scintillation in response to interacting with a received gamma photon. A first layer () is disposed in a first plane disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion () adjacent the first end surface and a reflective portion () adjacent the second end surface. A second layer () is disposed in a second plane orthogonal to the first plane and disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion () adjacent the second end surface and a reflective portion () adjacent the first end surface.

Pet detector scintillator arrangement with light sharing and depth of interaction estimation

A radiation detector is disclosed that includes a scintillation crystal and a plurality of photodetectors positioned to detect low-energy scintillation photons generated within the scintillation crystal. The scintillation crystals are processed using subsurface laser engraving to generate point-like defects within the crystal to alter the path of the scintillation photons. In one embodiment, the defects define a plurality of boundaries within a monolithic crystal to delineate individual detector elements. In another embodiment, the defects define a depth-of-interaction boundary that varies longitudinally to vary the amount of light shared by neighboring portions of the crystal. In another embodiment the defects are evenly distributed to reduce the lateral spread of light from a scintillation event. Two or more of these different aspects may be combined in a single scintillation crystal. Additionally, or alternatively, similar SSLE defects may be produced in other light-guiding elements of the radiation detector.

Optical-interface patterning for radiation detector crystals

A method for estimating a line or response in a positron emission tomography scanner having depth of interaction estimation capability. The method utilizes information from both detector modules detecting a coincident event. A joint probability density function combining factors accounting for intermediate Compton scattering interactions and/or a final interaction that may be either a Compton scattering interaction or photoelectric absorption is calculated. In a preferred embodiment, a Bayesian estimation scheme is used to integrate the PDF for all permutations of the measured signal pairs, and the permutation with the largest joint probability is selected to construct the estimated line of response.

Line of response estimation for high-resolution PET detector

Improved processing electronic hardware are disclosed that facilitate the efficient processing of PET system data, while enhancing accuracy and compatibility of PET systems with other analytical methods (e.g., magnetic resonance imaging). Improvements include the use of an application-specific integrated circuit (ASIC) for summing, by row, column, and diagonal, the output signals from an array of photodetectors in the PET system.

Data-processing electronics for use in a positron-emission tomography system

A method for estimating the start time of an electronic pulse generated in response to a detected event, for example the start time for pulses received in response to photon detection in positron emission tomography, includes providing a detector that detects an external event and generates an electronic analog pulse signal. A composite reference pulse curve is calculated to represent analog pulse signals generated by the detector. Upon receiving an analog pulse signal, it may be filtered, and then digitized, and normalized based on the area of the digital signal. Using at least one point of the normalized digital pulse signal, the composite reference pulse curve shape is used to estimate the pulse start time.

Data acquisition for positron emission tomography

A method for estimating the start time of an electronic pulse generated in response to a detected event, for example the start time for pulses received in response to photon detection in positron emission tomography, includes providing a detector that detects an external event and generates an electronic analog pulse signal. A parameterized ideal curve shape is selected to represent analog pulse signals generated by the detector. Upon receiving an analog pulse signal, it may be filtered, and then digitized, and normalized based on the area of the digital signal. Using at least one point of the normalized digital pulse signal, a curve from the parameterized ideal curve shape is selected, that best represents the received analog pulse signal, and the selected curve is used to estimate the pulse start time.

The invention disclosed herein is directed to scintillation detectors capable of detecting the position or depth of gamma photon interactions occurring within a scintillator, thereby improving the resolution of ring based positron emission tomography (PET) imaging systems. In one embodiment, the invention is directed to a scintillation detector that comprises at least one pair of side-by-side conjunct scintillation crystal bars having a shared interface between, and a solid-state semiconductor photodetector optically coupled to each output window of each individual scintillation crystal bar. The solid-state semiconductor photodetector includes an array of discrete sensitive areas disposed across a top surface of a common substrate, wherein each sensitive area contains an array of discrete micro-pixelated avalanche photodiodes, and wherein the output window of each scintillation crystal bar is optically coupled to each respective sensitive area in a one-on-one relationship.

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Shoreline, WA, United States of America

Robert S Miyaoka