Abstract: 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.

Abstract: 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.

Abstract: 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.

Abstract: 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.

Abstract: 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.

Abstract: 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.

Abstract: 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.

Abstract: 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×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.

Abstract: 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.

Abstract: 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×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.

Abstract: 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.

Abstract: 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.

Abstract: A Positron Emission Tomography (PET) tomograph having continuously rotating panel detectors. The PET tomograph includes two or more panel detector heads removably mounted on a rotating carriage system with a coincidence point source transmission system. Each panel detector head includes an array of scintillators, a light guide disposed behind the scintillators, and an array of detectors disposed behind the light guide. Each panel detector head further includes dedicated detector electronics for processing data collected from the detectors in that panel. Each detector block is comprised of an array of Lutetium Oxyorthosilicate (LSO) crystals. A rotational drive system is provided for continuously rotating the panel detector heads about the gantry frame. A data commutator is provided for communicating data from each detector panel head to a data processor. In order to remove heat generated by the panel detector heads, a chilled water cooling system is employed.

Abstract: A scintillation detector which includes a plurality of discrete scintillators composed of one or more scintillator materials. The discrete scintillators interact with incident radiation to produce a quantifiable number of photons with characteristic emission wavelength and decay time. A light guide is operatively associated with the scintillation crystals and may be either active or non-active and segmented or non-segmented depending upon the embodiment of the design. Photodetectors are provided to sense and quantify the scintillation light emissions. The process and system embodying various features of the present invention can be utilized in various applications such as SPECT, PET imaging and simultaneous PET systems.

Abstract: 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.

Abstract: 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.

Abstract: 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.

Abstract: 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.

Abstract: A combined positron emission tomography (PET) and computed tomography (CT) detector mounted on a single support on the same gantry of a combined PET and CT scanner. The common detector includes an array of scintillator crystals or pixels with each pixel mated to a photodetector. The photodetector is connected to discrete event circuitry, which provides discrete event information to the combined PET and CT scanner. Also, the photodetector is connected to integrating circuitry, which provides integrated count rate information to the CT scanner when the discrete event information is not adequate. By using a common detector, the registration of the PET image with the CT image is improved, less components are mounted on the gantry, the overall size of the gantry is reduced, resulting in a shorter tunnel and less rotating mass, and CT performance is enhanced by providing means for selecting the energy level of the x-rays to be detected.

Abstract: A transmission source serves to detect activity from a radiation source for correcting attenuation in either PET mode or SPECT mode. The transmission source includes a detector dedicated to collecting attenuation data in PET mode. A collimated radiation source and a detector are positioned with respect to a tomography device such that only a selected strip of the imaging detector of the tomograph is illuminated such that events unrelated to the attenuation are eliminated. The transmission source can either be a coincidence transmission source or a singles transmission source and includes a collimator in which is disposed a radiation source. An opening is defined by the collimator for exposing a selected portion of the imaging detectors of the tomograph device. Positioned behind the radiation source, relative to the imaging detectors, is the dedicated attenuation detector. In a dual head tomograph device, one transmission source of the present invention is disposed opposite each bank of imaging detectors.