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. 2021 May 10;49(10):2716–2733. doi: 10.1007/s10439-021-02785-0

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© The Author(s) 2021

Open AccessThis article is licensed under a Creative Commons Attribution 4.0 International License, which permits use, sharing, adaptation, distribution and reproduction in any medium or format, as long as you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons licence, and indicate if changes were made. The images or other third party material in this article are included in the article's Creative Commons licence, unless indicated otherwise in a credit line to the material. If material is not included in the article's Creative Commons licence and your intended use is not permitted by statutory regulation or exceeds the permitted use, you will need to obtain permission directly from the copyright holder. To view a copy of this licence, visit http://creativecommons.org/licenses/by/4.0/.

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Setup of the three experimental impact conditions carried out for each helmet (a). For each of the impacts, three translational and three rotational acceleration time-history pulses are recorded about the CoG of the HIII headform (b). These are then applied to the detailed finite element model of TBI (c) which is then further analysed to extract brain strain as an injury metric in regions-of-interest such as the corpus callosum and sulci (d). The three impacts were selected to produce different head rotations (a, b). Impact 1, with the initial position of the headform X-, Y- and Z-axis 0°, produces predominant rotation about the X-axis. For impact 2, the initial position of the headform was X-, Y-axis 0° and Z-axis -90°, which produces predominant rotation about the Y axis. For impact 3, the Initial position of the headform was X- and Z-axis 0° and 65° around Y-axis. This impact produces large rotation about the Z-axis compared to the other impacts.