Medtronic, Inc.

Other

Siemens Gammasonics, Inc.

Kms Fusion, Inc.

Glenn F Knoll

Donald R Strange

Matthew C Bennett, Jr

John C Engdahl

Timothy M Henderson

William L Rogers

Mark E Schrader

A gamma ray imaging detector for nuclear medical imaging includes an array of photodiode detectors provided on opposite surfaces of a scintillating crystal. By measuring the relative distribution of detection signal intensities produced by each photodiode in each array, it becomes possible to measure the depth of interaction of a gamma ray absorption event along the Z axis direction of the crystal in addition to its spatial position in the X-Y plane of the crystal and its absorption energy. The value of the measured depth of interaction is subsequently used in refining the calculation of the spatial location and improving the performance characteristics of the imaging detector.

Gamma ray imaging detector with three dimensional event positioning and

A gamma ray imaging detector is disclosed for use in nuclear medicine applications. The imaging detector includes a single scintillation detector crystal which converts absorbed gamma rays into a plurality of scintillation photons. The scintillation detector crystal emits scintillation light with a spectral distribution for which most of the yield corresponds to wavelengths longer than 475 nanometers and is preferably a thallium doped cesium iodide crystal. An array of photodiodes are arranged along one side of the crystal to receive the scintillation photons which generate an electrical output signal proportional to the number of scintillation photons received by the photodiode. Diodes with low capacitance and electrical noise, such as silicon drift photodiodes, are employed so that the signal generated by the photodiode as a result of the received scintillation photons is readily detectable above the electrical noise from the photodiodes. Electronic circuitry is then utilized to determine the position of impingement and absorption of the gamma ray.

Gamma ray imaging detector

A gamma ray scintillation camera generating (X,Y) spatial coordinate and Z energy signals relative to detected radiation events. The system provides for calibration of the camera Z signal response as a function of camera face location. The camera signals are converted to their digital equivalents subsequent to which the apparent coordinate locations of detected events as determined by the camera are corrected to their true spatial coordinates based upon correction information stored in the system.

Radiation signal processing system

A radiation-detection/scintillation composite in which a multiplicity of particulate glass carriers embodying radiation target nuclei are embedded within a matrix of solid scintillation plastic composition. The glass target-containing carriers have an index of refraction which closely matches that of the scintillation plastic. In one embodiment of the invention, the carriers comprise hollow spherical micro-size shells containing He-3 gas detection nuclei under pressure. In another embodiment, Li, B or Pb or other heavy element detection nuclei are contained within the composition of the glass carriers.

Radiation-detection/scintillator composite and method of manufacture

An improved method and apparatus for energy window selection in a radiation signal processing system which in a preferred embodiment includes obtaining energy level histograms corresponding to corrected spatial elements and determining a standard count of radiation events to be accepted by each true spatial element in response to a flood image. The energy window of each corrected spatial element is then adapted to cause each to accept the standard count of radiation events in response to a flood image whereby greater uniformity of image may be accomplished in the imaging process.

Energy window selection for a radiation signal processing system

A gamma ray scintillation camera generating (X,Y) spatial coordinate and Z energy signals relative to detected radiation events. The system provides for calibration of the camera Z signal response as a function of camera face location. In addition, the camera signals are converted to their digital equivalents subsequent to which the apparent coordinate locations of detected events as determined by the camera are corrected to their true spatial coordinates based upon correction information stored in the system.

A gamma ray scintillation camera generating (X,Y) spatial coordinate and Z energy signals relative to detected radiation events. The camera signals are converted to their digital equivalents subsequent to which the apparent coordinate locations of detected events as determined by the camera are corrected to their true spatial coordinates based upon correction information stored in the system. In addition to spatial coordinate correction, the system provides for calibration of the camera Z signal response as a function of camera face location.

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Ann Arbor, MI, United States of America

Glenn F Knoll