Practical considerations for noise power spectra estimation for clinical CT scanners
Local noise power spectra (NPS) have been commonly calculated to represent the noise properties of CT imaging systems, but their properties are significantly affected by the utilized calculation schemes. In this study, the effects of varied calculation parameters on the local NPS were analyzed, and...
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description | Local noise power spectra (NPS) have been commonly calculated to represent the noise properties of CT imaging systems, but their properties are significantly affected by the utilized calculation schemes. In this study, the effects of varied calculation parameters on the local NPS were analyzed, and practical suggestions were provided regarding the estimation of local NPS for clinical CT scanners. The uniformity module of a Catphan phantom was scanned with a Philips Brilliance 64 slice CT simulator with varied scanning protocols. Images were reconstructed using FBP and iDose4 iterative reconstruction with noise reduction levels 1, 3, and 6. Local NPS were calculated and compared for varied region of interest (ROI) locations and sizes, image background removal methods, and window functions. Additionally, with a predetermined NPS as a ground truth, local NPS calculation accuracy was compared for computer simulated ROIs, varying the aforementioned parameters in addition to ROI number. An analysis of the effects of these varied calculation parameters on the magnitude and shape of the NPS was conducted. The local NPS varied depending on calculation parameters, particularly at low spatial frequencies below ∼0.15 mm−1. For the simulation study, NPS calculation error decreased exponentially as ROI number increased. For the Catphan study the NPS magnitude varied as a function of ROI location, which was better observed when using smaller ROI sizes. The image subtraction method for background removal was the most effective at reducing low‐frequency background noise, and produced similar results no matter which ROI size or window function was used. The PCA background removal method with a Hann window function produced the closest match to image subtraction, with an average percent difference of 17.5%. Image noise should be analyzed locally by calculating the NPS for small ROI sizes. A minimum ROI size is recommended based on the chosen radial bin size and image pixel dimensions. As the ROI size decreases, the NPS becomes more dependent on the choice of background removal method and window function. The image subtraction method is most accurate, but other methods can achieve similar accuracy if certain window functions are applied. All dependencies should be analyzed and taken into account when considering the interpretation of the NPS for task‐based image quality assessment.
PACS number(s): 87.57.C‐, 87.57.Q‐ |
doi_str_mv | 10.1120/jacmp.v17i3.5841 |
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PACS number(s): 87.57.C‐, 87.57.Q‐</description><identifier>ISSN: 1526-9914</identifier><identifier>EISSN: 1526-9914</identifier><identifier>DOI: 10.1120/jacmp.v17i3.5841</identifier><identifier>PMID: 27167257</identifier><language>eng</language><publisher>United States: John Wiley & Sons, Inc</publisher><subject>Accuracy ; Algorithms ; background removal ; computed tomography ; Computer Simulation ; Humans ; Image Processing, Computer-Assisted - methods ; image quality assessment ; iterative CT reconstruction ; Medical Imaging ; Methods ; Noise ; noise power spectrum ; Optimization ; Phantoms, Imaging ; Quality ; Radiation therapy ; Scanners ; Signal-To-Noise Ratio ; Studies ; Tomography Scanners, X-Ray Computed ; Tomography, X-Ray Computed - methods</subject><ispartof>Journal of applied clinical medical physics, 2016-05, Vol.17 (3), p.392-407</ispartof><rights>2016 The Authors.</rights><rights>2016. This work is published under http://creativecommons.org/licenses/by/3.0/ (the “License”). Notwithstanding the ProQuest Terms and Conditions, you may use this content in accordance with the terms of the License.</rights><lds50>peer_reviewed</lds50><oa>free_for_read</oa><woscitedreferencessubscribed>false</woscitedreferencessubscribed><citedby>FETCH-LOGICAL-c4992-ae295c77741ae7666408264cc2f43f390869508ba1ba8e627a3a2116b900d6953</citedby><cites>FETCH-LOGICAL-c4992-ae295c77741ae7666408264cc2f43f390869508ba1ba8e627a3a2116b900d6953</cites></display><links><openurl>$$Topenurl_article</openurl><openurlfulltext>$$Topenurlfull_article</openurlfulltext><thumbnail>$$Tsyndetics_thumb_exl</thumbnail><linktopdf>$$Uhttps://www.ncbi.nlm.nih.gov/pmc/articles/PMC5690921/pdf/$$EPDF$$P50$$Gpubmedcentral$$Hfree_for_read</linktopdf><linktohtml>$$Uhttps://www.ncbi.nlm.nih.gov/pmc/articles/PMC5690921/$$EHTML$$P50$$Gpubmedcentral$$Hfree_for_read</linktohtml><link.rule.ids>230,314,723,776,780,860,881,1411,11542,27903,27904,45553,45554,46030,46454,53769,53771</link.rule.ids><backlink>$$Uhttps://www.ncbi.nlm.nih.gov/pubmed/27167257$$D View this record in MEDLINE/PubMed$$Hfree_for_read</backlink></links><search><creatorcontrib>Dolly, Steven</creatorcontrib><creatorcontrib>Chen, Hsin‐Chen</creatorcontrib><creatorcontrib>Anastasio, Mark</creatorcontrib><creatorcontrib>Mutic, Sasa</creatorcontrib><creatorcontrib>Li, Hua</creatorcontrib><title>Practical considerations for noise power spectra estimation for clinical CT scanners</title><title>Journal of applied clinical medical physics</title><addtitle>J Appl Clin Med Phys</addtitle><description>Local noise power spectra (NPS) have been commonly calculated to represent the noise properties of CT imaging systems, but their properties are significantly affected by the utilized calculation schemes. In this study, the effects of varied calculation parameters on the local NPS were analyzed, and practical suggestions were provided regarding the estimation of local NPS for clinical CT scanners. The uniformity module of a Catphan phantom was scanned with a Philips Brilliance 64 slice CT simulator with varied scanning protocols. Images were reconstructed using FBP and iDose4 iterative reconstruction with noise reduction levels 1, 3, and 6. Local NPS were calculated and compared for varied region of interest (ROI) locations and sizes, image background removal methods, and window functions. Additionally, with a predetermined NPS as a ground truth, local NPS calculation accuracy was compared for computer simulated ROIs, varying the aforementioned parameters in addition to ROI number. An analysis of the effects of these varied calculation parameters on the magnitude and shape of the NPS was conducted. The local NPS varied depending on calculation parameters, particularly at low spatial frequencies below ∼0.15 mm−1. For the simulation study, NPS calculation error decreased exponentially as ROI number increased. For the Catphan study the NPS magnitude varied as a function of ROI location, which was better observed when using smaller ROI sizes. The image subtraction method for background removal was the most effective at reducing low‐frequency background noise, and produced similar results no matter which ROI size or window function was used. The PCA background removal method with a Hann window function produced the closest match to image subtraction, with an average percent difference of 17.5%. Image noise should be analyzed locally by calculating the NPS for small ROI sizes. A minimum ROI size is recommended based on the chosen radial bin size and image pixel dimensions. As the ROI size decreases, the NPS becomes more dependent on the choice of background removal method and window function. The image subtraction method is most accurate, but other methods can achieve similar accuracy if certain window functions are applied. All dependencies should be analyzed and taken into account when considering the interpretation of the NPS for task‐based image quality assessment.
PACS number(s): 87.57.C‐, 87.57.Q‐</description><subject>Accuracy</subject><subject>Algorithms</subject><subject>background removal</subject><subject>computed tomography</subject><subject>Computer Simulation</subject><subject>Humans</subject><subject>Image Processing, Computer-Assisted - methods</subject><subject>image quality assessment</subject><subject>iterative CT reconstruction</subject><subject>Medical Imaging</subject><subject>Methods</subject><subject>Noise</subject><subject>noise power spectrum</subject><subject>Optimization</subject><subject>Phantoms, Imaging</subject><subject>Quality</subject><subject>Radiation therapy</subject><subject>Scanners</subject><subject>Signal-To-Noise Ratio</subject><subject>Studies</subject><subject>Tomography Scanners, X-Ray Computed</subject><subject>Tomography, X-Ray Computed - methods</subject><issn>1526-9914</issn><issn>1526-9914</issn><fulltext>true</fulltext><rsrctype>article</rsrctype><creationdate>2016</creationdate><recordtype>article</recordtype><sourceid>24P</sourceid><sourceid>EIF</sourceid><sourceid>ABUWG</sourceid><sourceid>AFKRA</sourceid><sourceid>AZQEC</sourceid><sourceid>BENPR</sourceid><sourceid>CCPQU</sourceid><sourceid>DWQXO</sourceid><sourceid>GNUQQ</sourceid><recordid>eNqFkc1LAzEQxYMoVqt3T7LgxUtrJtnNx0UoxS-o6KGeQ5pmNWWbrEmr-N8btyrqxdMMzG8e7_EQOgI8BCD4bKHNsh2-AHd0WIkSttAeVIQNpIRy-8feQ_spLTAGEFTsoh7hwDip-B6a3kdtVs7opjDBJze3Ua9c3oo6xMIHl2zRhlcbi9Ras4q6sGnllh3TIaZxvnsfT4tktPc2pgO0U-sm2cPP2UcPlxfT8fVgcnd1Mx5NBqaUkgy0JbIynPMStOWMsRILwkpjSF3SmkosmKywmGmYaWEZ4ZpqAsBmEuN5PtE-Ot_otuvZ0s6N9dlgo9qYDcY3FbRTvy_ePanH8KIqJrEkkAVOPwVieF7nZGrpkrFNo70N66SAC4lpxUuS0ZM_6CKso8_xFCHZkABGcabwhjIxpBRt_W0GsPqoTHWVqa4y9VFZfjn-GeL74aujDLAN8Ooa-_avoBqNbwmmktB3pWClBQ</recordid><startdate>20160508</startdate><enddate>20160508</enddate><creator>Dolly, Steven</creator><creator>Chen, Hsin‐Chen</creator><creator>Anastasio, Mark</creator><creator>Mutic, Sasa</creator><creator>Li, Hua</creator><general>John Wiley & Sons, Inc</general><general>John Wiley and Sons Inc</general><scope>24P</scope><scope>CGR</scope><scope>CUY</scope><scope>CVF</scope><scope>ECM</scope><scope>EIF</scope><scope>NPM</scope><scope>AAYXX</scope><scope>CITATION</scope><scope>3V.</scope><scope>7X7</scope><scope>7XB</scope><scope>88I</scope><scope>8FI</scope><scope>8FJ</scope><scope>8FK</scope><scope>ABUWG</scope><scope>AFKRA</scope><scope>AZQEC</scope><scope>BENPR</scope><scope>CCPQU</scope><scope>DWQXO</scope><scope>FYUFA</scope><scope>GHDGH</scope><scope>GNUQQ</scope><scope>HCIFZ</scope><scope>K9.</scope><scope>M0S</scope><scope>M2P</scope><scope>PIMPY</scope><scope>PQEST</scope><scope>PQQKQ</scope><scope>PQUKI</scope><scope>PRINS</scope><scope>Q9U</scope><scope>7X8</scope><scope>5PM</scope></search><sort><creationdate>20160508</creationdate><title>Practical considerations for noise power spectra estimation for clinical CT scanners</title><author>Dolly, Steven ; Chen, Hsin‐Chen ; Anastasio, Mark ; Mutic, Sasa ; Li, Hua</author></sort><facets><frbrtype>5</frbrtype><frbrgroupid>cdi_FETCH-LOGICAL-c4992-ae295c77741ae7666408264cc2f43f390869508ba1ba8e627a3a2116b900d6953</frbrgroupid><rsrctype>articles</rsrctype><prefilter>articles</prefilter><language>eng</language><creationdate>2016</creationdate><topic>Accuracy</topic><topic>Algorithms</topic><topic>background removal</topic><topic>computed tomography</topic><topic>Computer Simulation</topic><topic>Humans</topic><topic>Image Processing, Computer-Assisted - methods</topic><topic>image quality assessment</topic><topic>iterative CT reconstruction</topic><topic>Medical Imaging</topic><topic>Methods</topic><topic>Noise</topic><topic>noise power spectrum</topic><topic>Optimization</topic><topic>Phantoms, Imaging</topic><topic>Quality</topic><topic>Radiation therapy</topic><topic>Scanners</topic><topic>Signal-To-Noise Ratio</topic><topic>Studies</topic><topic>Tomography Scanners, X-Ray Computed</topic><topic>Tomography, X-Ray Computed - methods</topic><toplevel>peer_reviewed</toplevel><toplevel>online_resources</toplevel><creatorcontrib>Dolly, Steven</creatorcontrib><creatorcontrib>Chen, Hsin‐Chen</creatorcontrib><creatorcontrib>Anastasio, Mark</creatorcontrib><creatorcontrib>Mutic, Sasa</creatorcontrib><creatorcontrib>Li, Hua</creatorcontrib><collection>Wiley Online Library Open Access</collection><collection>Medline</collection><collection>MEDLINE</collection><collection>MEDLINE (Ovid)</collection><collection>MEDLINE</collection><collection>MEDLINE</collection><collection>PubMed</collection><collection>CrossRef</collection><collection>ProQuest Central (Corporate)</collection><collection>Health & Medical Collection</collection><collection>ProQuest Central (purchase pre-March 2016)</collection><collection>Science Database (Alumni Edition)</collection><collection>Hospital Premium Collection</collection><collection>Hospital Premium Collection (Alumni Edition)</collection><collection>ProQuest Central (Alumni) (purchase pre-March 2016)</collection><collection>ProQuest Central (Alumni Edition)</collection><collection>ProQuest Central UK/Ireland</collection><collection>ProQuest Central Essentials</collection><collection>ProQuest Central</collection><collection>ProQuest One Community College</collection><collection>ProQuest Central Korea</collection><collection>Health Research Premium Collection</collection><collection>Health Research Premium Collection (Alumni)</collection><collection>ProQuest Central Student</collection><collection>SciTech Premium Collection</collection><collection>ProQuest Health & Medical Complete (Alumni)</collection><collection>Health & Medical Collection (Alumni Edition)</collection><collection>Science Database</collection><collection>Publicly Available Content Database</collection><collection>ProQuest One Academic Eastern Edition (DO NOT USE)</collection><collection>ProQuest One Academic</collection><collection>ProQuest One Academic UKI Edition</collection><collection>ProQuest Central China</collection><collection>ProQuest Central Basic</collection><collection>MEDLINE - Academic</collection><collection>PubMed Central (Full Participant titles)</collection><jtitle>Journal of applied clinical medical physics</jtitle></facets><delivery><delcategory>Remote Search Resource</delcategory><fulltext>fulltext</fulltext></delivery><addata><au>Dolly, Steven</au><au>Chen, Hsin‐Chen</au><au>Anastasio, Mark</au><au>Mutic, Sasa</au><au>Li, Hua</au><format>journal</format><genre>article</genre><ristype>JOUR</ristype><atitle>Practical considerations for noise power spectra estimation for clinical CT scanners</atitle><jtitle>Journal of applied clinical medical physics</jtitle><addtitle>J Appl Clin Med Phys</addtitle><date>2016-05-08</date><risdate>2016</risdate><volume>17</volume><issue>3</issue><spage>392</spage><epage>407</epage><pages>392-407</pages><issn>1526-9914</issn><eissn>1526-9914</eissn><abstract>Local noise power spectra (NPS) have been commonly calculated to represent the noise properties of CT imaging systems, but their properties are significantly affected by the utilized calculation schemes. In this study, the effects of varied calculation parameters on the local NPS were analyzed, and practical suggestions were provided regarding the estimation of local NPS for clinical CT scanners. The uniformity module of a Catphan phantom was scanned with a Philips Brilliance 64 slice CT simulator with varied scanning protocols. Images were reconstructed using FBP and iDose4 iterative reconstruction with noise reduction levels 1, 3, and 6. Local NPS were calculated and compared for varied region of interest (ROI) locations and sizes, image background removal methods, and window functions. Additionally, with a predetermined NPS as a ground truth, local NPS calculation accuracy was compared for computer simulated ROIs, varying the aforementioned parameters in addition to ROI number. An analysis of the effects of these varied calculation parameters on the magnitude and shape of the NPS was conducted. The local NPS varied depending on calculation parameters, particularly at low spatial frequencies below ∼0.15 mm−1. For the simulation study, NPS calculation error decreased exponentially as ROI number increased. For the Catphan study the NPS magnitude varied as a function of ROI location, which was better observed when using smaller ROI sizes. The image subtraction method for background removal was the most effective at reducing low‐frequency background noise, and produced similar results no matter which ROI size or window function was used. The PCA background removal method with a Hann window function produced the closest match to image subtraction, with an average percent difference of 17.5%. Image noise should be analyzed locally by calculating the NPS for small ROI sizes. A minimum ROI size is recommended based on the chosen radial bin size and image pixel dimensions. As the ROI size decreases, the NPS becomes more dependent on the choice of background removal method and window function. The image subtraction method is most accurate, but other methods can achieve similar accuracy if certain window functions are applied. All dependencies should be analyzed and taken into account when considering the interpretation of the NPS for task‐based image quality assessment.
PACS number(s): 87.57.C‐, 87.57.Q‐</abstract><cop>United States</cop><pub>John Wiley & Sons, Inc</pub><pmid>27167257</pmid><doi>10.1120/jacmp.v17i3.5841</doi><tpages>16</tpages><oa>free_for_read</oa></addata></record> |
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subjects | Accuracy Algorithms background removal computed tomography Computer Simulation Humans Image Processing, Computer-Assisted - methods image quality assessment iterative CT reconstruction Medical Imaging Methods Noise noise power spectrum Optimization Phantoms, Imaging Quality Radiation therapy Scanners Signal-To-Noise Ratio Studies Tomography Scanners, X-Ray Computed Tomography, X-Ray Computed - methods |
title | Practical considerations for noise power spectra estimation for clinical CT scanners |
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