Koninklijke Philips Corporation N.v.

Koninklijke Philips Electronics N.v.

Philips Intellectual Property & Standards Gmbh

Manoj Narayanan

Jinghan Ye

Zhiqiang Hu

Andriy Andreyev

Xiyun Song

Bin Zhang

Lothar Spies

Bart Jacob Bakker

Jens-Christoph Georgi

Frank O Thiele

Yu-Lung Hsieh

Daniel Gagnon

Herfried Karl Wieczorek

Chuanyong Bai

Andreas Goedicke

Alexander Fischer

Pedro Jorge Da Silva Rodrigues

Andre Frank Salomon

Ralph Brinks

Andreia Maria Araujo Trindade Rodrigues

Amy Perkins

Michael Perkuhn

Bart Bakker

A time of flight (TOF) positron emission tomography (PET) image () is generated from TOF PET imaging data () acquired of a subject using a TOF PET imaging data acquisition device (). Iterative image reconstruction () of the TOF PET imaging data is performed with TOF localization of counts along respective lines of response (LORs) to iteratively update a reconstructed image (). Values for at least one regularization or filtering parameter are assigned to the TOF PET imaging data or to voxels of the reconstructed image based on an estimated TOF localization resolution for the TOF PET imaging data or voxels. Regularization () or filtering () of the reconstructed image is performed using the assigned values for the at least one regularization or filtering parameter. In some embodiments, the varying TOF localization resolution for the TOF PET imaging data or voxels is estimated based on related acquisition characteristics such as count rates or operating temperature of the detectors.

Time-of-flight resolution-adaptive image regularization and filtering in positron emission tomography

A radioemission scanner () is operated to acquire tomographic radioemission data of a radiopharmaceutical in a subject in an imaging field of view (FOV). An imaging system is operated to acquire extension imaging data of the subject in an extended FOV disposed outside of and adjacent the imaging FOV along an axial direction (). A distribution of the radiopharmaceutical in the subject in the extended FOV is estimated based on the extension imaging data, and further based on a database () of reference subjects. The tomographic radioemission data are reconstructed to generate a reconstructed image () of the subject in the imaging FOV. The reconstruction includes correcting the reconstructed image for scatter from the extended FOV into the imaging FOV based on the estimated distribution of the radiopharmaceutical in the subject in the extended FOV.

Outside-FOV activity estimation using surview and prior patient data in positron emission tomography

A medical system () for normalization correction of an imaging system () includes a detector geometry correction unit (), a crystal efficiency unit (), and a normalization unit (). The detector geometry correction unit () mathematically calculates a detector geometry correction component for a type of scanner () of interest. The crystal efficiency unit () configured to empirically determine a crystal efficiency component for at least one individual scanner (). The normalization unit () generates a normalization data set () which corresponds to a normalization correction factor of the at least one individual scanner () in accordance with the detector geometry correction component and the crystal efficiency component.

Hybrid method based on simulation and experimental data to normalize pet data

When estimating an arterial input function or a patient under study, cross-calibration factors are generated by comparing nuclear scan data of a radioactive material (e.g., F18) and measuring a sample of the radioactive material in a gamma counter. The derived cross-calibration factors are applied to venous samples collected from the patient during a nuclear scan after infusion with a radioactive tracer, to convert gamma values counted by the gamma counter into concentration values. The concentration values are used to optimize an initial estimated input function, thereby generating an arterialized input function.

Integrated work-flow for accurate input function estimation

A method includes generating a kinetic parameter value for a VOI in a functional image of a subject based on motion corrected projection data using an iterative algorithm, including determining a motion correction for projection data corresponding to the VOI based on the VOI, motion correcting the projection data corresponding to the VOI to generate the motion corrected projection data, and estimating the at least one kinetic parameter value based on the motion corrected projection data or image data generated with the motion corrected projection data. In another embodiment, a method includes registering functional image data indicative of tracer uptake in a scanned patient with image data from a different imaging modality, identifying a VOI in the image based on the registered images, generating at least one kinetic parameter for the VOI, and generating a feature vector including the at least one generated kinetic parameter and at least one bio-marker.

Functional imaging

A nuclear imaging system includes a scanner (), such as a PET scanner. A patient is injected with a [N]ammonia radioisotope tracer which is contaminated with a small percent ofF contamination. The scanner receives radiation from the injected tracer and a reconstruction processor () reconstructs the detected radiation into image representations. A calibration processor () generates an estimated decay curve based on the proton bombardment and a priori information about the tracer. An activity meter () measures radiation emitted from a sample of the tracer and a dose calibrator () determines a decay curve from the measured radiation. The detected radiation is corrected with one of the decay curves during reconstruction or a correction processor () corrects reconstructed images with one or both of the decay curves. A display () displays uncorrected reconstructed images and the decay curve and/or the corrected images.

Dynamic PET imaging with isotope contamination compensation

A method within dynamic molecular imaging comprising dynamically estimating a first parameter (&#x3b2;(x)) and a second parameter (k(x)) of an activity function describing the bio distribution of an administered tracer, is disclosed. More specifically, the method comprises specifying a first target variance (&#x3c3;(x)) and a second target variance (&#x3c3;(x)) of the first parameter (&#x3b2;(x)) and the second parameter (k(x)) of the activity function, respectively; initiating an image acquisition; reconstructing the first parameter (&#x3b2;(x)) and the second parameter (k(x)); reconstructing a first associated variance (&#x3c3;(x)) and a second associated variance (&#x3c3;(x)) of the first parameter (&#x3b2;(x)) and the second parameter (k(x)), respectively; and repeating the image acquisition and the reconstructing until the first associated variance (&#x3c3;(x)) and the second associated variance (&#x3c3;(x)) are equal to or less than the first target variance (&#x3c3;(x)) and the second target variance (&#x3c3;(x)), respectively, &#x3c3;(x)&#x2266;&#x3c3;(x) and &#x3c3;(x)&#x2266;&#x3c3;(x). The method enables patient-specific adaptive protocols within molecular imaging.

Method to individualize kinetic parameter estimation for dynamic molecular imaging procedures

An imaging system () comprises a data device (), which controls radiation data acquisition from a subject positioned in an examination region () for an examination. A rebinning processor () bins the acquired data periodically into a histogram (). A transform () transforms the histogram () into individual independent or uncorrelated components, each component including a signal content and a noise content. A stopping determining device () compares an aspect of at least one selected component to a predetermined threshold (TH) and, based on the comparison, terminates the data acquisition.

Patient scan time optimization for PET/SPECT imaging

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Snohomish, WA, United States of America

Manoj Narayanan