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In the above-referenced study, kinematic response data of various body regions were reported. The response data for the left shoulder was incorrect, as it was in fact the right wrist. In this corrigendum, the corrected kinematic response data for the left shoulder is presented. This encompasses the individual kinematic responses and corridors, the statistical analysis and the implications on the discussion and conclusion.

The choice of a human body model for a simulated automotive impact scenario must take into account both accurate model response and computational efficiency as key factors. This study presents a “modular numerical human body modeling” approach which allows the creation of a customized human body model of a 50th percentile male (size and weight), where the various body parts are modeled with different levels of complexity (multi-body and finite element) and can be easily swapped depending on the application. Implementation of this modeling technique has been performed by modularizing the MADYMO facet human body model, with focus on the pelvis and legs. Two component models have been attached: (1) a detailed facet pelvis and leg model of increased complexity, and (2) a full finite element pelvis and leg model. All models were subjected to various pendulum impacts for validation of the modular components and analysis of the resulting computational benefits.

Rapidly developing application areas for human models in simulations are pre-crash, rollover, comfort and occupant sensing, which in general require longer simulation times than the short impact scenarios used so far. These applications require postural stability of the human model during the simulated time, which was incorporated in the spine of the MADYMO human model in this study. The model uses lumped active control elements with full-state feedback at each vertebra in flexion-extension and lateral bending. Control parameters were identified on the basis of impactor tests on human volunteers. As a result a stable and robust model was developed, yet only the parameter identification did not live up to the expectations, due to limitations in both test and human model.

Both frontal and side air bags can inflict injuries to the upper extremities in cases where the limb is close to the air bag module at the time of impact. Current dummy limbs show qualitatively correct kinematics under air bag loading, but they lack biofidelity in long bone bending and fracture. Thus, an effective research tool is needed to investigate the injury mechanisms involved in air bag loading and to judge the improvements of new air bag designs. The objective of this study is to create an efficient numerical model that exhibits both correct global kinematics as well as localized tissue deformation and initiation of fracture under various impact conditions. The development of the model includes the creation of a sufficiently accurate finite element mesh, the adaptation of material properties from literature into constitutive models and the definition of kinematic constraints at articular joint locations.