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Computed Tomography III. Reconstruction Image quality Artifacts. Simple backprojection. Starts with an empty image matrix, and the  value from each ray in all views is added to each pixel in a line through the image corresponding to the ray’s path

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Computed Tomography III


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    1. Computed Tomography III Reconstruction Image quality Artifacts

    2. Simple backprojection • Starts with an empty image matrix, and the  value from each ray in all views is added to each pixel in a line through the image corresponding to the ray’s path • A characteristic 1/r blurring is a byproduct • A filtering step is therefore added to correct this blurring

    3. Filtered backprojection • The raw view data are mathematically filtered before being backprojected onto the image matrix • Involves convolving the projection data with a convolution kernel • Different kernels are used for varying clinical applications such as soft tissue imaging or bone imaging

    4. Convolution filters • Lak filter increases amplitude linearly as a function of frequency; works well when there is no noise in the data • Shepp-Logan filter incorporates some roll-off at higher frequencies, reducing high-frequency noise in the final CT image • Hamming filter has even more pronounced high-frequency roll-off, with better high-frequency noise suppression

    5. Bone kernels and soft tissue kernels • Bone kernels have less high-frequency roll-off and hence accentuate higher frequencies in the image at the expense of increased noise • For clinical applications in which high spatial resolution is less important than high contrast resolution – for example, in scanning for metastatic disease in the liver – soft tissue kernels are used • More roll-off at higher frequencies and therefore produce images with reduced noise but lower spatial resolution

    6. CT numbers or Hounsfield units • The number CT(x,y) in each pixel, (x,y), of the image is: • CT numbers range from about –1,000 to +3,000 where –1,000 corresponds to air, soft tissues range from –300 to –100, water is 0, and dense bone and areas filled with contrast agent range up to +3,000

    7. CT numbers (cont.) • CT numbers are quantitative • CT scanners measure bone density with good accuracy • Can be used to assess fracture risk • CT is also quantitative in terms of linear dimensions • Can be used to accurately assess tumor volume or lesion diameter

    8. Digital image display • Window and level adjustments can be made as with other forms of digital images • Reformatting of existing image data may allow display of sagittal or coronal slices, albeit with reduced spatial resolution compared with the axial views • Volume contouring and surface rendering allow sophisticated 3D volume viewing

    9. Image quality • Compared with x-ray radiography, CT has significantly worse spatial resolution and significantly better contrast resolution • Limiting spatial resolution for screen-film radiography is about 7 lp/mm; for CT it is about 1 lp/mm • Contrast resolution of screen-film radiography is about 5%; for CT it is about 0.5%

    10. Image quality (cont.) • Contrast resolution is tied to the SNR, which is related to the number of x-ray quanta used per pixel in the image • There is a compromise between spatial resolution and contrast resolution • Well-established relationship among SNR, pixel dimensions (), slice thickness (T), and radiation dose (D):

    11. Factors affecting spatial resolution • Detector pitch (center-to-center spacing) • For 3rd generation scanners, detector pitch determines ray spacing; for 4th generation scanners, it determines view sampling • Detector aperture (width of active element) • Use of smaller detectors improves spatial resolution • Number of views • Too few views results in view aliasing, most noticeable toward the periphery of the image

    12. Factors affecting spatial resolution (cont.) • Number of rays • For a fixed FOV, the number of rays increases as detector pitch decreases • Focal spot size • Larger focal spots cause more geometric unsharpness and reduce spatial resolution • Object magnification • Increased magnification amplifies the blurring of the focal spot

    13. Factors affecting spatial resolution (cont.) • Slice thickness • Large slice thicknesses reduce spatial resolution in the cranial-caudal axis; they also reduce sharpness of edges of structures in the transaxial image • Slice sensitivity profile • A more accurate descriptor of slice thickness • Helical pitch • Greater pitches reduce resolution. A larger pitch increases the slice sensitivity profile

    14. Factors affecting spatial resolution (cont.) • Reconstruction kernel • Bone filters have the best spatial resolution, and soft tissue filters have lower spatial resolution • Pixel matrix • Patient motion • Involuntary motion or motion resulting from patient noncompliance will blur the CT image proportional to the distance of motion during scan • Field of view • Influences the physical dimensions of each pixel

    15. Factors affecting contrast resolution • mAs • Directly influences the number of x-ray photons used to produce the CT image, thereby influencing the SNR and the contrast resolution • Dose • Dose increases linearly with mAs per scan • Pixel size (FOV) • If patient size and all other scan parameters are fixed, as FOV increases, pixel dimensions increase, and the number of x-rays passing through each pixel increases

    16. Factors affecting contrast resolution (cont.) • Slice thickness • Thicker slices uses more photons and have better SNR • Reconstruction filter • Bone filters produce lower contrast resolution, and soft tissue filters improve contrast resolution • Patient size • For the same technique, larger patients attenuate more x-rays, resulting in detection of fewer x-rays. Reduces SNR and therefore the contrast resolution

    17. Factors affecting contrast resolution (cont.) • Gantry rotation speed • Most CT systems have an upper limit on mA, and for a fixed pitch and a fixed mA, faster gantry rotations result in reduced mAs used to produce each CT image, reducing contrast resolution

    18. Beam hardening • Like all medical x-ray beams, CT uses a polyenergetic x-ray spectrum • X-ray attenuation coefficients are energy dependent • After passing through a given thickness of patient, lower-energy x-rays are attenuated to a greater extent than higher-energy x-rays are • As the x-ray beam propagates through a thickness of tissue and bones, the shape of the spectrum becomes skewed toward higher energies

    19. Beam hardening (cont.) • The average energy of the x-ray beam becomes greater (“harder”) as it passes through tissue • Because the attenuation of bone is greater than that of soft tissue, bone causes more beam hardening than an equivalent thickness of soft tissue

    20. Beam hardening (cont.) • The beam-hardening phenomenon induces artifacts in CT because rays from some projection angles are hardened to a differing extent than rays from other angles, confusing the reconstruction algorithm • Most scanners include a simple beam-hardening correction algorithm, based on the relative attenuation of each ray • More sophisticated two-pass algorithms determine the path length that each ray transits through bone and soft tissue, and then compensates each ray for beam hardening for the second pass

    21. Motion artifacts • Motion artifacts arise when the patient moves during the acquisition • Small motions cause image blurring • Larger physical displacements produce artifacts that appear as double images or image ghosting

    22. Partial volume averaging • Some voxels in the image contain a mixture of different tissue types • When this occurs, the  is not representative of a single tissue but instead is a weighted average of the different  values • Most pronounced for softly rounded structures that are almost parallel to the CT slice

    23. Partial volume averaging (cont.) • Occasionally a partial volume artifact can mimic pathological conditions • Several approaches to reducing partial volume artifacts • Obvious approach is to use thinner CT slices • When a suspected partial volume artifact occurs with a helical study and the raw scan data is still available, additional CT images may be reconstructed at different positions