Simone B. Bortolami

Localization of the subjective vertical during roll, pitch, and recumbent yaw body tilt

Localization of the subjective vertical during body tilt in pitch and in roll has been extensively studied because of the relevance of these axes for aviation and control of posture. Studies of yaw orientation relative to gravity are lacking. Our goal was to perform the first thorough evaluation of static orientation in recumbent yaw and to collect as efficiently as possible roll and pitch orientation data which would be consistent with the literature, using the same technique as our yaw tests. This would create the first comprehensive, coherent data set for all three axes suitable for quantitative tri-dimensional modeling of spatial orientation. We tested localization of the vertical for subjects tilted in pitch (−100° to +130°), in roll (−90° to +90°), and in yaw while recumbent (−80° to +80°). We had subjects point a gravity-neutral probe to the gravitational vertical (haptically indicated vertical) and report verbally their perceived tilt. Subjects underestimated their body tilts in recumbent yaw and pitch and overestimated their tilts in roll. The haptic settings for pitch and roll were consistent with data in the literature obtained with haptic and visual indications. Our data constitute the first tri-dimensional assessment of the subjective vertical using a common measurement procedure and provide the basis for the tri-axial modeling of vestibular function presented in the companion paper.

Mechanisms of human static spatial orientation

We have developed a tri-axial model of spatial orientation applicable to static 1g and non-1g environments. The model attempts to capture the mechanics of otolith organ transduction of static linear forces and the perceptual computations performed on these sensor signals to yield subjective orientation of the vertical direction relative to the head. Our model differs from other treatments that involve computing the gravitoinertial force (GIF) vector in three independent dimensions. The perceptual component of our model embodies the idea that the central nervous system processes utricular and saccular stimuli as if they were produced by a GIF vector equal to 1g, even when it differs in magnitude, because in the course of evolution living creatures have always experienced gravity as a constant. We determine just two independent angles of head orientation relative to the vertical that are GIF dependent, the third angle being derived from the first two and being GIF independent. Somatosensory stimulation is used to resolve our vestibular model’s ambiguity of the up–down directions. Our otolith mechanical model takes into account recently established non-linear behavior of the force–displacement relationship of the otoconia, and possible otoconial deflections that are not co-linear with the direction of the input force (cross-talk). The free parameters of our model relate entirely to the mechanical otolith model. They were determined by fitting the integrated mechanical/perceptual model to subjective indications of the vertical obtained during pitch and roll body tilts in 1g and 2g force backgrounds and during recumbent yaw tilts in 1g. The complete data set was fit with very little residual error. A novel prediction of the model is that background force magnitude either lower or higher than 1g will not affect subjective vertical judgments during recumbent yaw tilt. These predictions have been confirmed in recent parabolic flight experiments.

Kinetic analysis of arm reaching movements during voluntary and passive rotation of the torso

Reaching movements made to targets during exposure to passive constant velocity rotation show significant endpoint errors. By contrast, reaching movements made during voluntary rotation of the torso are accurate. In both cases, as a consequence of the simultaneous motion of the arm and the torso, Coriolis forces are generated on the arm tending to deflect its path. Our goal in the present paper was to determine whether during voluntary torso rotations arm movement accuracy is preserved by feed forward compensations for self-generated Coriolis forces. To test this hypothesis we analyzed and quantified the contribution of torso rotation and translation to arm dynamics and compared the kinematics and kinetics of pointing movements during voluntary and passive torso rotation. Coriolis torques at the shoulder increase nearly sixfold in voluntary turn and reach movements relative to reaches made without torso rotation, yet are equally accurate. Coriolis torques during voluntary turn and reach movements are more than double those produced by reaching movements during passive body rotation at 60°/s. Nevertheless, the endpoints of the reaches made during voluntary rotation are not deviated, but those of reaches made during passive rotation are deviated in the direction of the Coriolis forces generated during the movements. We conclude that there is anticipatory pre-programmed compensation for self-generated Coriolis forces during voluntary torso rotation contingent on intended torso motion and arm trajectory.

Dynamics model for analyzing reaching movements during active and passive torso rotation

We have developed an inverse dynamics model of unrestrained natural reaching movements. Such movements are usually not planar and often involve complex deformation of the shoulder girdle as well as rotary and linear torso motion. Our model takes as its input kinematic data about the positions of the finger, wrist, elbow, left and right acromion processes, and the sternum and produces the torques and forces developed at the shoulder, elbow, and wrist joints. The model can also be used to simulate the consequences of introducing passive torso rotation or linear acceleration on arm movements and to simulate the consequences of applying mechanical perturbations to the reaching limb. It separately quantifies the contributions of inertial forces resulting from torso rotation and translation. In experimental paradigms involving arm movements, different dynamic components can be present such as active or passive torso rotation and translation, external forces and Coriolis forces. Our model provides a means of evaluating the different sources of force and the total muscle force needed to control the trajectory of the arm in their presence.