Dual-energy-based metal segmentation for metal artifact reduction in dental computed tomography.

Autor: Hegazy MAA; Department of Biomedical Engineering, Kyung Hee University, 1732 Deogyeong-daero, Yongin-si, Gyeonggi-do, 446-701, Korea., Eldib ME; Department of Biomedical Engineering, Kyung Hee University, 1732 Deogyeong-daero, Yongin-si, Gyeonggi-do, 446-701, Korea., Hernandez D; Department of Biomedical Engineering, Kyung Hee University, 1732 Deogyeong-daero, Yongin-si, Gyeonggi-do, 446-701, Korea., Cho MH; Department of Biomedical Engineering, Kyung Hee University, 1732 Deogyeong-daero, Yongin-si, Gyeonggi-do, 446-701, Korea., Cho MH; Department of Biomedical Engineering, Kyung Hee University, 1732 Deogyeong-daero, Yongin-si, Gyeonggi-do, 446-701, Korea., Lee SY; Department of Biomedical Engineering, Kyung Hee University, 1732 Deogyeong-daero, Yongin-si, Gyeonggi-do, 446-701, Korea.
Jazyk: angličtina
Zdroj: Medical physics [Med Phys] 2018 Feb; Vol. 45 (2), pp. 714-724. Date of Electronic Publication: 2018 Jan 02.
DOI: 10.1002/mp.12719
Abstrakt: Purpose: In a dental CT scan, the presence of dental fillings or dental implants generates severe metal artifacts that often compromise readability of the CT images. Many metal artifact reduction (MAR) techniques have been introduced, but dental CT scans still suffer from severe metal artifacts particularly when multiple dental fillings or implants exist around the region of interest. The high attenuation coefficient of teeth often causes erroneous metal segmentation, compromising the MAR performance. We propose a metal segmentation method for a dental CT that is based on dual-energy imaging with a narrow energy gap.
Methods: Unlike a conventional dual-energy CT, we acquire two projection data sets at two close tube voltages (80 and 90 kV p ), and then, we compute the difference image between the two projection images with an optimized weighting factor so as to maximize the contrast of the metal regions. We reconstruct CT images from the weighted difference image to identify the metal region with global thresholding. We forward project the identified metal region to designate metal trace on the projection image. We substitute the pixel values on the metal trace with the ones computed by the region filling method. The region filling in the metal trace removes high-intensity data made by the metallic objects from the projection image. We reconstruct final CT images from the region-filled projection image with the fusion-based approach. We have done imaging experiments on a dental phantom and a human skull phantom using a lab-built micro-CT and a commercial dental CT system.
Results: We have corrected the projection images of a dental phantom and a human skull phantom using the single-energy and dual-energy-based metal segmentation methods. The single-energy-based method often failed in correcting the metal artifacts on the slices on which tooth enamel exists. The dual-energy-based method showed better MAR performances in all cases regardless of the presence of tooth enamel on the slice of interest. We have compared the MAR performances between both methods in terms of the relative error (REL), the sum of squared difference (SSD) and the normalized absolute difference (NAD). For the dental phantom images corrected by the single-energy-based method, the metric values were 95.3%, 94.5%, and 90.6%, respectively, while they were 90.1%, 90.05%, and 86.4%, respectively, for the images corrected by the dual-energy-based method. For the human skull phantom images, the metric values were improved from 95.6%, 91.5%, and 89.6%, respectively, to 88.2%, 82.5%, and 81.3%, respectively.
Conclusions: The proposed dual-energy-based method has shown better performance in metal segmentation leading to better MAR performance in dental imaging. We expect the proposed metal segmentation method can be used to improve the MAR performance of existing MAR techniques that have metal segmentation steps in their correction procedures.
(© 2017 American Association of Physicists in Medicine.)
Databáze: MEDLINE
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