• We are sorry, but NCBI web applications do not support your browser and may not function properly. More information
Logo of springeropenLink to Publisher's site
Annals of Biomedical Engineering
Ann Biomed Eng. May 2011; 39(5): 1563–1569.
Published online Jan 11, 2011. doi:  10.1007/s10439-010-0240-y
PMCID: PMC3071943

Sensitivity of Local Dynamic Stability of Over-Ground Walking to Balance Impairment Due to Galvanic Vestibular Stimulation

Abstract

Impaired balance control during gait can be detected by local dynamic stability measures. For clinical applications, the use of a treadmill may be limiting. Therefore, the aim of this study was to test sensitivity of these stability measures collected during short episodes of over-ground walking by comparing normal to impaired balance control. Galvanic vestibular stimulation (GVS) was used to impair balance control in 12 healthy adults, while walking up and down a 10 m hallway. Trunk kinematics, collected by an inertial sensor, were divided into episodes of one stroll along the hallway. Local dynamic stability was quantified using short-term Lyapunov exponents (λs), and subjected to a bootstrap analysis to determine the effects of number of episodes analysed on precision and sensitivity of the measure. λs increased from 0.50 ± 0.06 to 0.56 ± 0.08 (p = 0.0045) when walking with GVS. With increasing number of episodes, coefficients of variation decreased from 10 ± 1.3% to 5 ± 0.7% and the number of p values >0.05 from 42 to 3.5%, indicating that both precision of estimates of λs and sensitivity to the effect of GVS increased. λs calculated over multiple episodes of over-ground walking appears to be a suitable measure to calculate local dynamic stability on group level.

Keywords: Galvanic vestibular stimulation, Gait stability, Lyapunov exponents, Nonlinear dynamics, Accidental falls, Local dynamic stability

Introduction

Recently, there has been a growing interest in quantifying gait stability using a method based on nonlinear time series analysis, i.e., local dynamic stability.1113 Local dynamic stability is defined by “maximum finite-time Lyapunov exponents”, which describe how the system’s states respond to very small perturbations continuously in real time.10,13,28 It has been suggested that dynamic stability of gait can be of clinical use,30 specifically in identifying elderly at risk of falling, since it was shown to differentiate between older adults with and without a history of falls.24

Precise estimation of Lyapunov exponents theoretically requires at least 10n data points, with n being the dimension of the attractor, and improves with the number of “cycles” captured by those data points.28 In a recent study, we showed that for human gait data, limited increases in precision were obtained when using data series longer than 150 strides (sampled at 50 samples/s).6 A convenient method of continuously collecting data over many successive strides is to use a treadmill. Unfortunately, such large number of strides may not be feasible for frail elderly or patient populations and treadmills are relatively expensive instruments. Recently it was shown that inertial sensor data can be used as an alternative to optoelectronic data for calculation of Lyapunov exponents of trunk kinematics during gait.5 This would allow for data collection in the typical clinical setting where gait is assessed on a short walkway. Using inertial sensor data collected during over-ground walking, where speed can not be controlled exactly and where the Lyapunov exponent is calculated over multiple short episodes, would make this measure more applicable, e.g., to diagnose elderly at risk of falling. However, it is unknown if this would compromise the precision of the measure and its ability to detect impaired balance control (sensitivity). In addition, although statistical precision of estimates will by definition increase monotonically with sample size (i.e., more episodes), the magnitude of the increase in precision cannot be predicted in a straightforward manner, such as in sampling from a normally distributed population, because consecutive episodes may not represent independent samples.

Sensitivity of local dynamic stability measures estimated from multiple short episodes of over-ground walking at preferred walking speed can be investigated by comparing normal to impaired balance control. Balance control can be impaired in young adults by randomly varying galvanic vestibular stimulation (GVS). Specifically, the firing rates of the vestibular afferents are decreased or increased by the anodal and cathodal currents of GVS,2 resulting in an observable, adjustable sway in the lateral direction during walking.3,16 It is shown that in subjects facing forward, bipolar binaural stochastic GVS leads to coherent stochastic mediolateral postural sway.26 Therefore, stochastic GVS is suggested to quantitatively and qualitatively model instability of vestibular origin.25,26,29

Recently, it was shown that local dynamic stability measures can detect the impairment of balance control induced by GVS during treadmill walking at several walking speeds, including preferred walking speed, in young adults.33 The present study used bootstrap analyses to quantify the increase in precision of estimates of local dynamic stability as a function of number of episodes used for analysis. In addition, we tested the hypothesis that GVS would cause a decrease in local dynamic stability in over-ground walking. Finally, we quantified the effect of number of episodes analyzed on sensitivity to the GVS-induced balance impairment at the group and individual level.

Materials and Methods

Subjects

Ten subjects (7 males and 3 females; mean age 23 ± 2.6 years; height 1.8 ± 0.1 m; and mass 76.3 ± 12.5 kg) participated in the study. Exclusion criteria were any orthopedic or neurological disorders, or other injuries that could interfere with gait. Alcohol consumption was prohibited for 24 h prior to testing. Subjects filled in a medical intake form and signed informed consent. The protocol was approved by the Local Ethical Committee.

Materials

Portable wireless inertial sensor nodes (Xsens, Xsens Technology, Enschede, The Netherlands), which include 3D gyroscopes and accelerometers, were attached at the back of the trunk over the spine at the level of T6. Data-acquisition (50 samples/s) was done with MT Manager (version 1.5.0, Xsens Technology, Enschede, The Netherlands), and analyses were performed using MATLAB (version 7.5, The MathWorks BV, Natick, MA, USA).

To apply GVS, flexible, carbon electrodes were attached with electroconductive adhesive gel (Tac Gel™) over the mastoid bones. GVS was applied binaurally and bipolarly to each subject by a computer controlled galvanic stimulator (IDEE, Maastricht University, Maastricht, The Netherlands). To prevent adaptation, the galvanic stimulus was composed of a linear summation of sinusoids with five different frequencies (0.02, 0.07, 0.11, 0.30, and 0.50 Hz), all starting at a phase of 0 degrees and each having a maximum amplitude of 0.6 mA. This pseudo-random stimulus had a maximum amplitude of about 2.2 mA, irrespective of the electrical conductivity of the skin and temporal bone.

Procedure

Prior to the measurement, the reaction of subjects to GVS was tested, although no negative psychological or mental side effects are known from literature,2,19 following which the subjects were familiarized with the sensation of GVS for about 20 s. Some subjects reported a slightly dizzy feeling or a weak stinging under the electrodes. The dizziness disappeared after a few seconds and the stinging was remedied by reattaching the electrode.

Measurements were performed during over-ground walking at preferred walking speed, walking up and down an approximately 3 m wide and 10 m long hallway. Each trial, both with and without GVS, lasted 3 min and included on average 20 turns. Participants were instructed to look straight ahead, since GVS induces a body sway lateral to the orientation of the head, regardless of the body orientation.34

Pre-processing

For each trial, time series of 9000 samples (3 min) were obtained. These data were analyzed without filtering, because of the complications associated with applying linear filters to nonlinear signals.11,12 For each subject, the data were divided into episodes, each episode representing a one-way stroll of 7 strides along the hallway without a turn. The walking speed was calculated for each episode, based on the known walking distance and time elapsed between turns. To exclude the influence of data series length on local dynamic stability measures,6,15 for each episode a fixed number of 7 continuous strides was time normalized by shape-preserving piecewise cubic interpolation to 350 total samples, i.e., an average of 50 points per cycle. Note that this implied almost no creation or reduction of data points given a sampling rate of 50 samples/s and an average stride time of 1.08 s.

Quantifying Local Dynamic Stability

The calculation of maximum Lyapunov exponents to qualify local dynamic stability requires constructing a states space from measured data. Although several studies used five-dimensional state spaces,6,10,15 based on embedding reconstruction methods31 we preferred a biomechanical state space consisting of 12 dimensions. This 12D state space was reconstructed from the 3D angular velocities along with the 3D linear accelerations of the trunk and their time-delayed copies.5,18 A standard time delay of 12 samples was used for the time-delayed copies, which roughly corresponds to the derivatives. This approach was first proposed by Kang and Dingwell,20 who reasoned that a 3D free body has a total of 12 state variables (i.e., 3D positions, velocities, orientations, and angular velocities). Recently, it was shown that such an approach yielded results closest to the expected value for a known system, and was most sensitive to differences between conditions.17

Maximum Lyapunov exponents represent the exponential rate of divergence from nearest neighbor points on adjacent trajectories in the reconstructed state space, and thus the response to small local perturbations of the system.11 Positive exponents indicate local dynamic instability, with larger exponents demonstrating an increased sensitivity to local perturbations,11 while values <0 indicate local dynamic stability.

To calculate maximum Lyapunov exponents, Euclidian distances between neighboring trajectories in state space were computed as a function of time and averaged over all original pairs of initial nearest neighbors. The short-term Lyapunov exponent (λs) was calculated from the slopes of linear fits to the first 0–0.5 stride of the log of these divergence curves, rather than to 0–1 stride, since the divergence curve has been found to be nonlinear after about 75 samples (Fig. 1).7 In addition, a recent study has demonstrated that λs based on a single step was related to the probability of falling in a passive dynamic walking model and could therefore be successfully used to predict stability.8

Figure 1
Examples of divergence curves and the corresponding short-term Lyapunov exponents (λs), for walking with GVS (dashed line) and without GVS (dashed-dotted line)

It should be noted that the region where the slope was fitted may not be fully linear, and the exponent found may thus not be a “true” Lyapunov exponent. However, it still provides a well-defined metric for estimating the sensitivity of human walking to small intrinsic perturbations.10,21 In addition, this λs (i.e., calculated from 0 to 0.5 strides) has been shown to discriminate fall prone elderly from elderly without a history of falling.24

Bootstrapping

A bootstrapping procedure4 was used to assess the statistical precision of λs as a function of number of episodes. Bootstrap analysis can be used for statistical inferences without requiring assumptions on distribution of the data. For introductory texts see Zhu.35 In addition, bootstrap analysis can be used to support decision making on sample size (Efron and Tibshirani14), as has been done for biomechanical variables previously (e.g., van Dieën et al.32; Bruijn et al.6). These previous applications usually considered nested bootstrap analyses which allow inferences on effects of for example number of subjects measured as well as number of measurements per subject. In the present study bootstrap analyses were performed ‘within subjects’, since our main focus was on clinical application.

First, λs was calculated for each subject and for each of the 16 episodes of 7 strides per condition. Next, for every subject, a sample of a number (n) of randomly selected episodes was drawn (with n ranging from 3 to 12) for both conditions. A maximum sample size of n = 12 out of 16 episodes was used, to avoid too much overlap between the bootstrap samples and thus an overestimate of the statistical precision. This procedure was repeated 1000 times for every n.

To express statistical precision of the estimate of λs, the coefficient of variation (COV), defined as the standard deviation over the 1000 samples normalized to the mean was calculated for each sample of n episodes.

To examine the sensitivity of λs to GVS-induced balance impairment as a function of number of episodes at group level, a paired t test was performed over sample means of all subjects between the two conditions. In addition, for each individual subject, an unpaired t test between the two samples (one normal walking selection of n episodes, and one GVS selection of n episodes) was performed, to quantify sensitivity at the individual level. Finally, both for the individual and group level comparisons, the percentage of the 1000 t test results with p values above 0.05 was calculated.

Results

All subjects produced the required 16 episodes of 7 strides. The mean walking speed was 1.31 m/s (SD 0.25) when walking with GVS and 1.35 m/s (SD 0.26) without GVS. In addition, the mean standard deviations between episodes within subjects were 0.080 (SD 0.024) with GVS and 0.083 (SD 0.020) without GVS. No significant difference between the two conditions was found for either the mean walking speed (p = 0.149) or the within-subject standard deviation (p = 0.768).

Averaged over all 16 episodes, λs was higher for walking with GVS compared to walking without GVS for most of the subjects (Fig. 2). At the group level, λs significantly increased from a mean of 0.50 (SD 0.06) during normal walking to a mean of 0.56 (SD 0.08) when walking with GVS (p = 0.0045), indicating a decreased local dynamic stability when walking with GVS.

Figure 2
Scatter plot of the short-term Lyapunov exponents (λs) for each subject, averaged over all 12 episodes for the conditions with and without GVS. Error bars represent the standard deviation and the diagonal line is the identity line

Although GVS affected λs at the group level, this effect was less apparent at the individual level. Whereas walking with GVS showed higher values for most subjects when averaged over all 16 episodes, a substantial variation of λs over episodes existed within each subject for both conditions (see for an example Fig. 3).

Figure 3
Variation of the short-term Lyapunov exponents (λs) calculated for different episodes of one typical subject

Therefore, the effect of averaging λs over a varying number of episodes for each subject on the precision was examined by a bootstrapping procedure. As expected, the COVs decreased monotonically with an increasing number of episodes (Fig. 4). For walking with GVS, the COV decreased from 10% (SD 1.3) when using 3 episodes to 5% (SD 0.7) for 12 episodes. Without GVS, the decrease was from 11% (SD 3.1) to 5% (SD 1.4). The increase in precision above 11 episodes was limited.

Figure 4
The coefficient of variation over 1000 estimates of the short-term Lyapunov exponent for different numbers of episodes averaged over all subjects for both walking with (asterisk) and without (triangle) GVS. Error bars represent standard error

In addition, the effect of averaging λs over a varying number of episodes on the sensitivity was studied. At the group level, a clear decrease in number of p values >0.05, indicating an increase in sensitivity, with increasing number of episodes was found (Fig. 5) with percentages of p values >0.05 decreasing from 42.0% when using 3 episodes to 3.5% for 12 episodes.

Figure 5
Bootstrapping results at group level of the percentage of p values >0.05 (paired t test), comparing walking with and without GVS, for the different numbers of episodes

However, on the individual level, the effect of increasing number of episodes on sensitivity varied strongly (Fig. 6). Five subjects showed less than 20% improvement in sensitivity to GVS when using 12 episodes compared to 3 episodes, whereas the other five subjects showed improvements of 27% up to 78%.

Figure 6
Individual bootstrapping results of the percentage of p values >0.05 (unpaired t test), comparing walking with and without GVS, for the different numbers of episodes

Discussion

In search for methods that would allow the use of the maximum Lyapunov exponent as a measure of balance impairments in clinical situations, we studied the effects of different numbers of short episodes of over-ground walking data on the precision and sensitivity of λs. We found a significant effect of GVS on λs at group level, with higher values when GVS was applied, indicating that λs was able to detect the imposed balance impairment during over-ground walking. However, this effect was less apparent at the individual level. This might be due to the fact that our healthy young subjects responded differently to GVS, but our statistical design was not aimed to evaluate individual responses to GVS. Nevertheless, we showed that averaging over a larger numbers of episodes led to a considerable increase in precision, leading to sufficient sensitivity at the group level but not at the individual level.

Walking speed influences local dynamic stability of walking.7,12,15 However, no significant differences in mean walking speed or within-subject variance of speed were found in this study between the two conditions. Therefore, the differences in local dynamic stability found between the two conditions are most likely not the result of variation in walking speed between trials, although speed fluctuations within episodes could not be determined.

Multiple Episodes

Various studies have described the influence of time series length and the number of strides on maximum Lyapunov exponents and have suggested that trial lengths of 150 strides or more are needed for precise estimates of the Lyapunov exponent.6,21 However, these large numbers of strides are required when one single trial is measured, and both Bruijn et al.6 and Kang and Dingwell21 have suggested that measuring several trials may increase precision. The decrease of COV and p values >0.05 with an increasing number of episodes found in the current study indicate that precision and sensitivity can be improved by using multiple episodes, instead of using large numbers of consecutive strides. It should be noted that perhaps not the “true” Lyapunov exponent is found, since the region where the slope was fitted may not have been fully linear. However, the used λs proved sensitive to small intrinsic perturbations10 and able to discriminate fall prone elderly from healthy elderly.24

A large range of mean λs values (λS = 0.06–3) has been reported in literature.6,7,10,13 The mean values found in the current study were approximately λs = 0.60 and fall within the same range, but are small compared with most of the reported values of λs previously mentioned. The relative low values may be explained by the small number of strides used in the calculations: nearest neighbors that lay far apart cannot diverge far and in longer data series the nearest neighbor will tend to be closer.6 In addition, different definitions of the state space, timescales used for the calculation of λs, or number of embedding dimensions may lead to different values of λs.17

The Effect of GVS on Local Dynamic Stability

The effect of GVS on λs found in the current study is in agreement with expectations, since GVS is known to cause instabilities in the mediolateral direction.16,34 The same direction also appears affected by aging,27 suggesting a similarity between the effects of GVS and of aging on balance control. In addition, the effects of both GVS and aging include higher values of λs.24,33 According to the literature, the estimated differences in λs between older and young adults are within the range of Δλs = 10–50%.9,2224 When comparing fall prone and healthy elderly, the estimated difference is Δλs = 10–20%.18,24 In the current study and the previously mentioned study of van Schooten et al.,33 the mean difference due to the effect of GVS was Δλs = 10%. Although walking speed and conditions (treadmill and over-ground walking) varied in the above-mentioned studies,1,7,13,15 this suggests that instabilities induced by GVS are probably smaller than those induced by aging and that age-related effects are even more likely to be detected by maximum Lyapunov exponents.

Implications of the Current Study

The purpose of the study was to find a clinically applicable method to detect balance impairments using local dynamic stability measures. The results showed that an increase in precision of λs may be gained by measuring multiple short trials during normal over-ground walking. Therefore, no additional equipment is needed to study walking stability in a clinical setting and limitations caused by low endurance of patients can partially be overcome by using multiple short walking trials. Moreover, the measure can be assessed with a single inertial sensor on the trunk, which is portable, small, reasonably cheap, and straightforward to utilize, since it does not have to be aligned with a global coordinate system.5 However, the resulting precision and sensitivity of λs at 12 episodes was still insufficient to detect the effect of GVS in each individual subject. Nevertheless, since the effect of GVS on gait stability appeared relatively small compared to reported effects of aging and pathology, sensitivity to age-related or pathological balance impairments merits further study.

Overall, the presented effect of using multiple episodes on the precision and sensitivity of λs suggests that this measure is suitable for scientific purposes involving group level analysis. However, future studies should address the sensitivity of local dynamic stability of gait to differences in fall risk among older adults.

Acknowledgments

The authors acknowledge Warner ten Kate for the support and trial versions of the inertial sensors and Josien van der Noort for assistance with the inertial sensors. Mirjam Pijnappels and Kim van Schooten were financially supported by a TOP-NIG grant (#91209021) from The Netherlands Organization for Scientific Research (NWO). Sjoerd Bruijn was partly funded by a grant from Biomet Nederland.

Open Access This article is distributed under the terms of the Creative Commons Attribution Noncommercial License which permits any noncommercial use, distribution, and reproduction in any medium, provided the original author(s) and source are credited.

References

1. Alton F, Baldey L, Caplan S, Morrissey MC. A kinematic comparison of overground and treadmill walking. Clin. Biomech. (Bristol, Avon) 1998;13:434–440. doi: 10.1016/S0268-0033(98)00012-6. [PubMed] [Cross Ref]
2. Balter SGT, Stokroos RJ, Jong I, Bouwmans R, Laan M, Kingma H. Background on methods of stimulation in galvanic-induced body sway in young healthy adults. Acta Otolaryngol. 2004;124:262–271. doi: 10.1080/00016480310015245. [PubMed] [Cross Ref]
3. Bent LR, McFadyen BJ, Merkley VF, Kennedy PM, Inglis JT. Magnitude effects of galvanic vestibular stimulation on the trajectory of human gait. Neurosci. Lett. 2000;279(3):157–160. doi: 10.1016/S0304-3940(99)00989-1. [PubMed] [Cross Ref]
4. Briggs AH, Wonderling DE, Mooney CZ. Pulling cost-effectiveness analysis up by its bootstraps: a non-parametric approach to confidence interval estimation. Health Econ. 1997;6(4):327–340. doi: 10.1002/(SICI)1099-1050(199707)6:4<327::AID-HEC282>3.0.CO;2-W. [PubMed] [Cross Ref]
5. Bruijn SM, Haeck J, Dieën JH, ten Kate WRT, Meijer OG, Beek PJ. Estimates of stability measures using data from non aligned inertial sensors. Ann. Biomed. Eng. 2008;38(8):2588–2593. doi: 10.1007/s10439-010-0018-2. [PMC free article] [PubMed] [Cross Ref]
6. Bruijn SM, Dieën JH, Meijer OG, Beek PJ. Statistical precision and sensitivity of measures of dynamic gait stability. J. Neurosci. Methods. 2009;178:327–333. doi: 10.1016/j.jneumeth.2008.12.015. [PubMed] [Cross Ref]
7. Bruijn SM, Dieen JH, Meijer OG, Beek PJ. Is slow walking more stable? J. Biomech. 2009;42(10):1506–1512. doi: 10.1016/j.jbiomech.2009.03.047. [PubMed] [Cross Ref]
8. Bruijn, S. M., D. J. J. Bregman, O. G. Meijer, P. J. Beek, and J. H. van Dieen. The validity of stability measures: a modelling approach. In: 16th US National Congress on Theoretical and Applied Mechanics, University Park, Pennsylvania, USA, 2010.
9. Buzzi UH, Stergiou N, Kurz MJ, Hageman PA, Heidel J. Nonlinear dynamics indicates aging affects variability during gait. Clin. Biomech. 2003;18:435–443. doi: 10.1016/S0268-0033(03)00029-9. [PubMed] [Cross Ref]
10. Dingwell JB, Cusomano JP. Nonlinear time series analysis of normal and pathological human walking. Chaos. 2000;10:848–863. doi: 10.1063/1.1324008. [PubMed] [Cross Ref]
11. Dingwell JB, Kang HG. Differences between local and orbital dynamic stability during human walking. J. Biomech. Eng. 2007;129(4):586–593. doi: 10.1115/1.2746383. [PubMed] [Cross Ref]
12. Dingwell JB, Marin LC. Kinematic variability and local dynamic stability of upper body motions when walking at different speeds. J. Biomech. 2006;39(3):444–452. [PubMed]
13. Dingwell JB, Cusumano JP, Cavanagh PR, Sternad D. Local dynamic stability versus kinematic variability of continuous overground and treadmill walking. J. Biomech. Eng. 2001;123(1):27–32. doi: 10.1115/1.1336798. [PubMed] [Cross Ref]
14. Efron B, Tibshirani R. Bootstrap methods for standard errors, confidence intervals, and other measures of statistical accuracy. Stat. Sci. 1986;1:54–77. doi: 10.1214/ss/1177013815. [Cross Ref]
15. England SA, Granata KP. The influence of gait speed on local dynamic stability of walking. Gait Posture. 2007;25:172–178. doi: 10.1016/j.gaitpost.2006.03.003. [PMC free article] [PubMed] [Cross Ref]
16. Fitzpatrick RC, Wardman DL, Taylor JL. Effects of galvanic vestibular stimulation during human walking. J. Physiol. 1999;517(Pt 3):931–939. doi: 10.1111/j.1469-7793.1999.0931s.x. [PMC free article] [PubMed] [Cross Ref]
17. Gates DH, Dingwell JB. Comparison of different state space definitions for local dynamic stability analyses. J. Biomech. 2009;42(9):1345–1349. doi: 10.1016/j.jbiomech.2009.03.015. [PMC free article] [PubMed] [Cross Ref]
18. Granata KP, Lockhart TE. Dynamic stability differences in fall-prone and healthy adults. J. Electromyogr. Kinesiol. 2008;18:172–178. doi: 10.1016/j.jelekin.2007.06.008. [PMC free article] [PubMed] [Cross Ref]
19. Jahn K, Strupp M, Schneider E, Dieterich M, Brandt T. Differential effects of vestibular stimulation on walking and running. Neuroreport. 2000;11:1745–1748. doi: 10.1097/00001756-200006050-00029. [PubMed] [Cross Ref]
20. Kang HG, Dingwell JB. A direct comparison of local dynamic stability during unperturbed standing and walking. Exp. Brain Res. 2006;172(1):35–48. doi: 10.1007/s00221-005-0224-6. [PubMed] [Cross Ref]
21. Kang HG, Dingwell JB. Intra-session reliability of local dynamical stability of walking. Gait Posture. 2006;24:286–290. doi: 10.1016/j.gaitpost.2005.11.004. [PubMed] [Cross Ref]
22. Kang HG, Dingwell JB. Effects of walking speed, strength and range of motion on gait stability in healthy older adults. J. Biomech. 2008;41:2899–2905. doi: 10.1016/j.jbiomech.2008.08.002. [PubMed] [Cross Ref]
23. Kang HG, Dingwell JB. Dynamic stability of superior vs. inferior segments during walking in young and older adults. Gait Posture. 2009;30:260–263. doi: 10.1016/j.gaitpost.2009.05.003. [PMC free article] [PubMed] [Cross Ref]
24. Lockhart TE, Lui J. Differentiating fall-prone and healthy adults using local dynamic stability. Ergonomics. 2008;51:1860–1872. doi: 10.1080/00140130802567079. [PMC free article] [PubMed] [Cross Ref]
25. MacDougall HG, Moore ST, Curthoys IS, Black FO. Modeling postural instability with Galvanic vestibular stimulation. Exp. Brain Res. 2006;172(2):208–220. doi: 10.1007/s00221-005-0329-y. [PubMed] [Cross Ref]
26. Pavlik AE, Inglis JT, Lauk M, Oddsson L, Collins JJ. The effects of stochastic galvanic vestibular stimulation on human postural sway. Exp. Brain Res. 1999;124(3):273–280. doi: 10.1007/s002210050623. [PubMed] [Cross Ref]
27. Rogers MW, Mille ML. Lateral stability and falls in older people. Exerc. Sport Sci. Rev. 2003;31:182–187. doi: 10.1097/00003677-200310000-00005. [PubMed] [Cross Ref]
28. Rosenstein M, Collins JJ, Luca CJ. A practical method for calculating largest Lyapunov exponents from small data sets. Phys. D. 1993;65:117–134. doi: 10.1016/0167-2789(93)90009-P. [Cross Ref]
29. Scinicariello AP, Eaton K, Inglis JT, Collins JJ. Enhancing human balance control with galvanic vestibular stimulation. Biol. Cybern. 2001;84(6):475–480. doi: 10.1007/PL00007991. [PubMed] [Cross Ref]
30. Segal AD, Orendurff MS, Czerniecki JM, Shofer JB, Klute GK. Local dynamic stability of amputees wearing a torsion adapter compared to a rigid adapter during straight-line and turning gait. J. Biomech. 2010;43(14):2798–2803. doi: 10.1016/j.jbiomech.2010.05.038. [PubMed] [Cross Ref]
31. Takens F. Detecting strange attractors in turbulence. In: Rand D, Young L-S, editors. Dynamical Systems and Turbulence, Warwick 1980. Berlin/Heidelberg: Springer; 1981. pp. 366–381.
32. Dieen JH, Hoozemans MJ, Beek AJ, Mullender M. Precision of estimates of mean and peak spinal loads in lifting. J. Biomech. 2002;35(7):979–982. doi: 10.1016/S0021-9290(02)00051-9. [PubMed] [Cross Ref]
33. van Schooten, K. S., L. H. Sloot, S. M. Bruijn, H. Kingma, O. G. Meijer, M. Pijnappels, and J. H. van Dieen. Sensitivity of trunk variability and stability measures to balance impairments induced by Galvanic Vestibular Stimulation during gait (submitted). [PubMed]
34. Wardman DL, Fitzpatrick RC. What does galvanic vestibular stimulation stimulate? Adv. Exp. Med. Biol. 2002;508:119–128. [PubMed]
35. Zhu W. Making bootstrap statistical inferences: a tutorial. Res. Q. Exerc. Sport. 1997;68(1):44–55. [PubMed]

Articles from Springer Open Choice are provided here courtesy of Springer

Formats:

Related citations in PubMed

See reviews...See all...

Cited by other articles in PMC

See all...

Links

  • MedGen
    MedGen
    Related information in MedGen
  • PubMed
    PubMed
    PubMed citations for these articles

Recent Activity

Your browsing activity is empty.

Activity recording is turned off.

Turn recording back on

See more...