A second reconstruction would then be carried out on the attenuation-corrected data. More advanced methods relied on segmenting various major structures from the emission sinogram (first Forskolin cost introduced for brain imaging [30]) to determine regions of soft tissue and bone, though these approaches failed in nonhomogeneous regions, resulting in overestimation of activity in regions adjacent to (for example) air cavities and thereby confounding interpretation of the resulting images. Consequently, methods that rely on transmission data have been developed. Transmission scanning (reviewed in Ref. [31]) is based on positioning radioactive sources just inside the detector

ring around the object to be imaged and collecting photons before (the so-called http://www.selleckchem.com/products/dabrafenib-gsk2118436.html “blank scan”) and after the object is placed in the scanner, allowing the total attenuation along each LOR to be directly measured. While this technique increases the accuracy of attenuation correction, it introduces statistical noise (from limited photon counts due to limited source strength) and adds to total scan time. However, with the development of dedicated PET–CT scanners, the transmission scan has been essentially replaced by using CT data to directly assign the linear attenuation coefficient on a voxel-by-voxel basis.

In this method, the Hounsfield units at the effective energy of the CT X-ray beam returned from the CT reconstruction are converted to linear attenuation coefficients for 511-keV photons (a conversion for single-energy CT studies not without its own assumptions) and then used to correct for attenuation of the emission photons. However, there is still the issue of misregistration as the CT data are not acquired simultaneously Thalidomide with the PET data, and this fundamentally limits the accuracy

a CT-based attenuation correction method can realize; errors of approximately 10% in the standardized uptake value (SUV) have been reported [32] and [33]. Though retrospective (software-based) image registration can correct for such errors if the object in unchanging, hardware-based registration in which the images are acquired simultaneously and therefore inherently registered, something of greater importance for thoracic and abdominal imaging than (say) for the head. Simultaneous PET–MRI offers the potential to eliminate this specific problem. There are, however, other concerns with the use of MRI for implementing accurate attenuation corrections. The signal intensity in standard MRI sequences is based on combinations of proton density and tissue relaxation properties — measurements that are not directly related to electron density and therefore not directly related to the linear attenuation coefficients of tissue.