{"status":"ok","message-type":"work","message-version":"1.0.0","message":{"indexed":{"date-parts":[[2026,9,1]],"date-time":"2026-09-01T22:39:14Z","timestamp":1788302354487,"version":"build-2803163510"},"reference-count":48,"publisher":"Wiley","issue":"1","license":[{"start":{"date-parts":[[2024,10,3]],"date-time":"2024-10-03T00:00:00Z","timestamp":1727913600000},"content-version":"vor","delay-in-days":0,"URL":"http:\/\/onlinelibrary.wiley.com\/termsAndConditions#vor"}],"content-domain":{"domain":["aapm.onlinelibrary.wiley.com"],"crossmark-restriction":true},"short-container-title":["Medical Physics"],"published-print":{"date-parts":[[2025,1]]},"abstract":"<jats:title>Abstract<\/jats:title><jats:sec><jats:title>Background<\/jats:title><jats:p>Photon counting detectors (PCDs) for x\u2010ray computed tomography (CT) are the future of CT imaging. At present, semiconductor\u2010based PCDs such as cadmium telluride (CdTe), cadmium zinc telluride, and silicon have been either used or investigated for clinical PCD CT. Unfortunately, all of them have the same major challenges, namely high cost and limited spectral signal\u2010to\u2010noise ratio (SNR). Recent studies showed that some high\u2010quality scintillators, such as lanthanum bromide doped with cerium (LaBr<jats:sub>3<\/jats:sub>:Ce), are less expensive and almost as fast as CdTe.<\/jats:p><\/jats:sec><jats:sec><jats:title>Purpose<\/jats:title><jats:p>The objective of this study is to assess the performance of a LaBr<jats:sub>3<\/jats:sub>:Ce PCD for clinical x\u2010ray CT.<\/jats:p><\/jats:sec><jats:sec><jats:title>Methods<\/jats:title><jats:p>We performed Monte Carlo simulations and compared the performance of 3 mm thick LaBr<jats:sub>3<\/jats:sub>:Ce and 2 mm thick CdTe for PCD CT with x\u2010rays at 120 kVp and 20\u20131000\u00a0mA. The two PCDs were operated with either a threshold\u2013subtract (TS) counting scheme or a direct energy binning (DB) counting scheme. The performance was assessed in terms of the accuracy of registered spectra, counting capability, and count\u2010rate\u2010dependent spectral imaging\u2010task performance, for conventional CT imaging, water\u2013bone material decomposition, and K\u2010edge imaging with tungsten as the K\u2010edge material. The performance for these imaging\u2010tasks was quantified by nCRLB, that is, the Cram\u00e9r\u2013Rao lower bound on the variance of basis line\u2010integral estimation, normalized by the corresponding value of CdTe at 20\u00a0mA.<\/jats:p><\/jats:sec><jats:sec><jats:title>Results<\/jats:title><jats:p>The spectrum recorded by CdTe was distorted significantly due to charge sharing, whereas the spectra recorded by LaBr<jats:sub>3<\/jats:sub>:Ce better matched the incident spectrum. The dead time, estimated by fitting a paralyzable detector model to the count\u2010rate curves, was 20.7, 15.0, 37.2, and 13.0\u00a0ns for CdTe with TS, CdTe with DB, LaBr<jats:sub>3<\/jats:sub>:Ce with TS, and LaBr<jats:sub>3<\/jats:sub>:Ce with DB, respectively. Conventional CT imaging showed an adverse effect of reduced geometrical efficiency due to optical reflectors in LaBr<jats:sub>3<\/jats:sub>:Ce PCD. The nCRLBs (a lower value indicates a better SNR) for CdTe with TS, CdTe with DB, LaBr<jats:sub>3<\/jats:sub>:Ce with TS, LaBr<jats:sub>3<\/jats:sub>:Ce with DB, and the ideal PCD, were 1.00\u00a0\u00b1\u00a00.01, 1.00\u00a0\u00b1\u00a00.01, 1.18\u00a0\u00b1\u00a00.02, 1.18\u00a0\u00b1\u00a00.02, and 0.79\u00a0\u00b1\u00a00.01, respectively, at 20\u00a0mA. The nCRLBs for water\u2013bone material decomposition, in the same order, were 1.00\u00a0\u00b1\u00a00.02, 1.00\u00a0\u00b1\u00a00.02, 0.85\u00a0\u00b1\u00a00.02, 0.85\u00a0\u00b1\u00a00.02, and 0.24\u00a0\u00b1\u00a00.02, respectively, at 20\u00a0mA; and 0.98\u00a0\u00b1\u00a00.02, 0.98\u00a0\u00b1\u00a00.02, 1.09\u00a0\u00b1\u00a00.02, 0.83\u00a0\u00b1\u00a00.02, and 0.24\u00a0\u00b1\u00a00.02, respectively, at 1000\u00a0mA. Finally, the nCRLBs for K\u2010edge imaging, the most demanding task among the five, were 1.00\u00a0\u00b1\u00a00.02, 1.00\u00a0\u00b1\u00a00.02, 0.55\u00a0\u00b1\u00a00.02, 0.55\u00a0\u00b1\u00a00.02, and 0.13\u00a0\u00b1\u00a00.02, respectively, at 20\u00a0mA; and 2.45\u00a0\u00b1\u00a00.02, 2.29\u00a0\u00b1\u00a00.02, 3.12\u00a0\u00b1\u00a00.02, 2.11\u00a0\u00b1\u00a00.02, and 0.13\u00a0\u00b1\u00a00.02, respectively, at 1,000\u00a0mA.<\/jats:p><\/jats:sec><jats:sec><jats:title>Conclusion<\/jats:title><jats:p>The Monte Carlo simulations showed that, compared to CdTe with either TS or DB, LaBr<jats:sub>3<\/jats:sub>:Ce with DB provided more accurate spectra, comparable or better counting capability, and superior spectral imaging\u2010task performances, that is, water\u2013bone material decomposition and K\u2010edge imaging. CdTe had a better performance than LaBr<jats:sub>3<\/jats:sub>:Ce for the conventional CT imaging task due to its higher geometrical efficiency. LaBr<jats:sub>3<\/jats:sub>:Ce PCD with DB scheme may be an excellent alternative option for CdTe PCD.<\/jats:p><\/jats:sec>","DOI":"10.1002\/mp.17436","type":"journal-article","created":{"date-parts":[[2024,10,3]],"date-time":"2024-10-03T12:48:37Z","timestamp":1727959717000},"page":"158-170","update-policy":"https:\/\/doi.org\/10.1002\/crossmark_policy","source":"Crossref","is-referenced-by-count":11,"title":["Imaging performance of a LaBr<sub>3<\/sub>:Ce scintillation detector for photon counting x\u2010ray computed tomography: Simulation study"],"prefix":"10.1002","volume":"52","author":[{"given":"Katsuyuki","family":"Taguchi","sequence":"first","affiliation":[{"name":"The Russell H. 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