Abstract: Fluorine-containing molecules include fluorine-18 labeled hydrogen ion indicator molecules and methods of making and using the same. Fluorine atoms incorporated into the indicator molecules provides novel structural modifications to the precursor molecules, shifting the absorbance maxima relative to their non-fluorinated precursor/cogeners. These molecules are useful for non-invasive in vivo measurement of blood volume, blood flow and pH in biological objects. Compounds are functionalized by a radioisotopically enriched fluorine-18 label and indicator molecule with structure derived from triarylmethane derived indicators, such as phenol red, cresol red, cresol purple, thymol blue, bromophenol red, naphthol blue, phenolphthalein, cresolphthalein, thymolphthalein, naphtholphthalein, gentian violet (methyl violet 10B), methyl violet 2B, methyl violet 6B, leucomalachite green (malachite green), brilliant green, pararosaniline, fuchsines, or salts thereof.

Abstract: Provided are time-of-flight positron emission tomography devices comprising a detector array having at least two segments configured to accommodate a body part and to acquire tracer emission signals from a target within an imaging situs with a timing resolution of less than about 600 ps and a processor that receives the acquired signals from the detector array and converts the signals into a three dimensional image reconstruction of the target.

Abstract: The invention relates to a collimation apparatus for use in biomedical imaging systems. Specifically, the invention relates to a collimation apparatus that blocks a portion of its crystal with a radiation blocking element.

Abstract: Provided are time-of-flight positron emission tomography devices comprising a detector array having at least two segments configured to accommodate a body part and to acquire tracer emission signals from a target within an imaging situs with a timing resolution of less than about 600 ps and a processor that receives the acquired signals from the detector array and converts the signals into a three dimensional image reconstruction of the target.

Abstract: A cylinder (10) of radiation detectors (12) in a diagnostic imaging apparatus detects radiation pairs with corresponding electronic detector channels (22) which have non-uniform time-varying temporal delays. A plurality of calibration radiation sources (20) that concurrently emit radiation pairs is mounted at known positions inside of the cylinder. A temporal correction processor (46) uses the known positions of the calibration sources to determine errors in the relative detection times of radiation pairs from the calibration sources and uses the determined errors to generate corrections for the relative detection times of radiation pairs from radiopharmaceuticals injected in an imaged subject.

Abstract: A cylinder (10) of radiation detectors (12) in a diagnostic imaging apparatus detects radiation pairs with corresponding electronic detector channels (22) which have non-uniform time-varying temporal delays. A plurality of calibration radiation sources (20) that concurrently emit radiation pairs is mounted at known positions inside of the cylinder A temporal correction processor (46) uses the known positions of the calibration sources to determine errors in the relative detection times of radiation pairs from the calibration sources and uses the determined errors to generate corrections for the relative detection times of radiation pairs from radiopharmaceuticals injected in an imaged subject.

Abstract: A Lanthanum Halide scintillator (for example LaCl3 and LaBr3) with fast decay time and good timing resolution, as well as high light output and good energy resolution, is used in the design of a PET scanner. The PET scanner includes a cavity for accepting a patient and a plurality of PET detector modules arranged in an approximately cylindrical configuration about the cavity. Each PET detector includes a Lanthanum Halide scintillator having a plurality of Lanthanum Halide crystals, a light guide, and a plurality of photomultiplier tubes arranged respectively peripherally around the cavity. The good timing resolution enables a time-of-flight (TOF) PET scanner to be developed that exhibits a reduction in noise propagation during image reconstruction and a gain in the signal-to-noise ratio.

Abstract: A Lanthanum Halide scintillator (for example LaCl3 and LaBr3) with fast decay time and good timing resolution, as well as high light output and good energy resolution, is used in the design of a PET scanner. The PET scanner includes a cavity for accepting a patient and a plurality of PET detector modules arranged in an approximately cylindrical configuration about the cavity. Each PET detector includes a Lanthanum Halide scintillator having a plurality of Lanthanum Halide crystals, a light guide, and a plurality of photomultiplier tubes arranged respectively peripherally around the cavity. The good timing resolution enables a time-of-flight (TOF) PET scanner to be developed that exhibits a reduction in noise propagation during image reconstruction and a gain in the signal-to-noise ratio.