Typically, balance training has been used as an intervention paradigm either as static or as reactive balance training. Possible differences in functional outcomes between the two modalities have not been profoundly studied. The objective of the study was to investigate the specificity of neuromuscular adaptations in response to two balance intervention modalities within test and intervention paradigms containing characteristics of both profiles: classical sensorimotor training (SMT) referring to a static ledger pivoting around the ankle joint vs. reactive balance training (RBT) using externally applied perturbations to deteriorate body equilibrium. Thirty-eight subjects were assigned to either SMT or RBT. Before and after four weeks of intervention training, postural sway and electromyographic activities of shank and thigh muscles were recorded and co-contraction indices (CCI) were calculated. We argue that specificity of training interventions could be transferred into corresponding test settings containing properties of SMT and RBT, respectively. The results revealed that i) postural sway was reduced in both intervention groups in all test paradigms; magnitude of changes and effect sizes differed dependent on the paradigm: when training and paradigm coincided most, effects were augmented (P<0.05). ii) These specificities were accompanied by segmental modulations in the amount of CCI, with a greater reduction within the CCI of thigh muscles after RBT compared to the shank muscles after SMT (P<0.05). The results clearly indicate the relationship between test and intervention specificity in balance performance. Hence, specific training modalities of postural control cause multi-segmental and context-specific adaptations, depending upon the characteristics of the trained postural strategy. In relation to fall prevention, perturbation training could serve as an extension to SMT to include the proximal segment, and thus the control of structures near to the body’s centre of mass, into training.
Citation: Freyler K, Krause A, Gollhofer A, Ritzmann R (2016) Specific Stimuli Induce Specific Adaptations: Sensorimotor Training vs. Reactive Balance Training. PLoS ONE 11(12): e0167557. https://doi.org/10.1371/journal.pone.0167557
Editor: Gayle E. Woloschak, Northwestern University Feinberg School of Medicine, UNITED STATES
Received: December 30, 2015; Accepted: November 16, 2016; Published: December 2, 2016
Copyright: © 2016 Freyler et al. This is an open access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.
Data Availability: All relevant data are contained within the paper.
Funding: This study was funded by the German Aerospace Center (DLR 50WB1120). The article processing charge was funded by the open access publication fund of the Albert-Ludwigs-University Freiburg. The funders had no role in study design, data collection and analysis, decision to publish, or preparation of the manuscript. This does not alter our adherence to PLOS ONE policies on sharing data and materials.
Competing interests: The authors have declared that no competing interests exist.
Balance training is widely applied in different settings of rehabilitative medicine , geriatrics [2,3] and as a training method for fall and injury prevention [4–6]. The generic term “balance training” comprises all exercises on instable or moveable surfaces in manifold training settings. Within this, typically two types of balance modality can be subdivided: static and reactive balancing. These two balance types can be classified according to their biomechanical constraints and differ in how instability is induced, thus they result in different motor strategies of compensating for dislocated masses: Importantly, SMT (executed on wobbling or tilt boards, soft mats, cushions, etc.; [7,8]) can mainly be characterized by a single inverted pendulum model [9–13]. Thereby, the relative mass which needs to be adjusted in regard to the gravitational vector is proportionally large, inducing large torques in the ankle joint. In reactive balance tasks, upright stance is perturbed via translations of support surface. According to perturbed stance, investigations support the concept of a double inverted or ‘multi-link’ pendulum [13–17], whereby during re-adjustment of the body the relative mass is distributed over several joints from the ankle up to the knee and hip joints.
Based on the biomechanical differences of the training modalities, we expect that SMT must not necessarily evoke similar functional and neuromuscular adaptations compared to RBT. Although no intervention studies exist comparing both balance modalities in one common experimental setting, there is evidence in literature that these two training stimuli may cause task-specific adaptations [18,19]. The essential differences in biomechanical characteristics and stabilizing strategies between SMT and RBT are described as follows.
- From a biomechanical point of view, interventions differ in regard to the “fixed point”, the pivot, and the “mobile point”, the moving components that are accelerated during the postural task: Comparing SMT to RBT, stabilizing torques are shifted from distal to proximal. The fixed point is exchanged from the ankle joint (SMT) to the centre of mass (COM) itself (RBT), and the “mobile point” in turn is exchanged from the whole body COM (SMT) to the feet (RBT) [9,10,13,15,20,21].
- COM stabilization requires different strategies. Studies investigating static stance refer to balance control focusing on the stabilization of the ankle joint with the target to stabilize the gravitational vector of the COM within small trajectories vertically above the feet [9,20–22]. In contrast, in response to perturbation, the COM is horizontally shifted, inducing larger horizontal head and trunk displacements [23–25]. Hence, RBT requires a multi-joint strategy involving a torso replacement to relocate the vector of the COM within broad critical trajectories adequately above the feet [10,16,26–28].
- The origin of the postural disturbance differs. In SMT, merely self-initiated disruptions of stability cause the neuromuscular system to generate corrective torques to move the vector of the COP in phase with the vector of the COM within the self-initiated frequency [9,29]. In RBT, postural disturbances are applied externally and equilibrium is disrupted by unexpected stimuli via application of unpredictable, random platform displacements [26,30–33].
Distinctions regarding the different training stimuli described in 1–3 are inevitably associated with peculiarities in neuromuscular control and the distribution of involved body segments. Hence, distinction can be drawn in terms of the specificity of the motor control strategy: Supported by literature, the main contributors to control the COM above the base of support in SMT are distal muscles encompassing the ankle joint [6,9,16,22,34]. Conversely, RBT requires an active re-positioning or “tracing” of the COM according to the feet translation, mainly executed by an intersegmental neuromuscular coordination pattern including thigh and hip muscles [28,35,36].
Based on the above-mentioned aspects, we expect that long-term exposure to SMT compared to RBT leads to highly task-specific adaptations. The rationale of this study was to verify the specificity of adaptations in response to these two balance training modalities based on a test-intervention paradigm. Figuring out such differences may be of significant relevance for the practical application of SMT and RBT in rehabilitation or prevention settings with an impact on balance training recommendations. For a conclusive statement, it was tested whether the specificity of training interventions could be depicted in various test paradigms by quantifying balance performance regarding neuromuscular adaptation, segmental involvement and changes in sway path. For this purpose, the postural requirement profile of each training intervention (SMT or RBT) corresponded with one particular test paradigm. To strengthen the study design, in a third test paradigm (transfer task) it should be tested whether specificity of adaptations is limited to the corresponding test paradigm itself [37–40], or if they can be transferred to another, not trained paradigm. We hypothesize that both regimens improve balance performance in all paradigms. However, we expect adaptations to be specific with particularly high effects in the respective paradigm in which postural demands coincide with the trained exercise. Equal effects for both groups are estimated when transfer skills are required in the transfer paradigm.
Materials and Methods
Thirty-nine healthy subjects (23 females, 15 males, 24±3years) participated in the study. The sample size was estimated by means of a power analysis (f = 0.25; alpha = 0.05; power = 0.90) prior to the experiment. Participants had no acute injuries or neurological irregularities and were not allowed to perform any balance training in addition to the study’s schedule during the period and for six months before the start of the experiment. All subjects gave written informed consent to the experimental procedure, which was approved by the ethics committee of the University of Freiburg in accordance with the latest revision of the Declaration of Helsinki. To provide comparable baseline values in both groups, participants were randomly divided by “matched-pairs” into either a reactive balance training group (RBT-group, 11 females, 8 males, 24±3years, height 173±7cm, weight 67±12kg), or a control group performing conventional sensorimotor training (SMT-group, 13 females, 7 males, 24±3years, height 172±9cm, weight 67±10kg). Matched pairs were built based on the postural sway measures (described in detail in the outcome measures). A pair of subjects with almost equivalent performance levels prior to training start was equally distributed to the SMT and RBT group.
Both biomechanical paradigms of the training interventions are described in Fig 1. Both training interventions lasted four weeks and comprised three sessions per week with a duration of twenty minutes each. One session comprised four sets separated by one minute rest interval: each set contained four repetitions, respectively. Each repetition lasted one minute and was divided into 40 seconds training/20 seconds intermittent rest interval . RBT was performed on an electromagnetically driven swinging platform (40x40cm, Perturmed®; for further information about the device, see ), generating random surface translations in the horizontal plane (Fig 1). To eliminate anticipation of perturbations during RBT, perturbations were randomly varied in (i) direction (medio-lateral [m-l], anterior-posterior [a-p] and diagonals), (ii) order of applied direction (not randomised vs. randomised), (iii) amplitude (2, 4, 6, 8cm), (iv) order of applied amplitude (not randomised vs. randomised), (v) duration of platform remaining in perturbed position (100, 275, 1500ms), (vi) pause length between perturbations (1, 2, 3, 4s), (vii) order of the pause length (not randomised vs. randomised), embracing a training matrix with 16 levels in total. The subjects had the instruction to stabilize equilibrium as fast as possible after perturbation. After the initial platform displacement, the platform described a damped sinus curve until subjects reached a stable equilibrium (within ~1.5s), before the next perturbation was triggered. SMT  was performed with conventional balance devices including unstable surfaces such as foam balance pads (Airex®) or balance cushions (Togu® Dynair air cushions ø33cm; Aero-Step cushions 51x37x8cm/46x32x8cm; Jumper® 52x24cm, BOSU® 67x65x22cm), so that the complexity of balance performance ranged from easy to more challenging postural demands. Subjects had the instruction to stand as still as possible. For both groups, the level of performance difficulty was increased gradually and individually during training by changing to a more challenging perturbation programme during RBT, such as increase of translation displacement, increase of additional directions, increase of the length of perturbation stimulus (holding the platform up to 1.5s at the perturbed end position) and reduction of durations between signals, or by changing to a more challenging support surface during SMT and subsequently by closing the eyes to exclude visual cues. All training sessions were surveyed, supervised and documented. Training was executed with the left leg. Training load of both interventions was matched regarding duration, frequency and rest interval of training periods and sessions.
During SMT, the center of mass (COM) needs to be kept as still as possible and stability is reached when the COM stays solidly with the body as an inverted pendulum rotating around the ankle joint. During RBT, after each perturbation of the support surface, the COM needs to be actively relocated through the proximal segment to keep a stable equilibrium.
The test-intervention specificity of adaptations in response to four weeks of SMT vs. RBT was evaluated on the basis of a longitudinal repeated-measures matched-subject design. We examined whether specificity of training interventions could be transferred into corresponding test settings. For this purpose, the postural requirement profile of each training intervention (SMT or RBT) corresponded with one particular test paradigm (protocol 1 and 2), a third protocol served as a transfer test (shown in Fig 2A). To strengthen the study design, we chose test settings that none of the groups had trained in.
(B) Changes in thigh (upper row) and shank (middle row) CCIs as well as COPml/postural sway (bottom row) in response to the training interventions SMT (grey square) and RBT (black triangle) in (A) the three different test paradigms on the spinning top (ST, left column), on the swinging platform (SP, middle column) and during the transfer condition with cognitive interference (CI, right column). Adaptations in all parameters were greater in the SMT-group than in the RBT-group for ST, whereas during SP, adaptations were greater in the RBT-group than in the SMT-group. For CI, a greater reduction in COPml displacement was observed in the RBT-group: it is assumed that the higher decrease in thigh CCI (dashed box) led to the better functional balance performance.
For all protocols, participants were balancing barefoot on the left leg and instructed to place their hands on their hips, direct their head and eyes forward and to stand as still as possible. Three trials of 30 seconds were performed for each protocol, separated by 30 seconds of rest. The order of the three protocols was conducted counter-balanced across participants but was identical for each subject for pre/post measurements; between each protocol, subjects rested for three minutes. Ankle, knee and hip joints were supervised visually to control the body position. To exclude habituation effects, prior to measurements subjects practised for a period of 10 minutes to adapt to the different surfaces. For the assessment of balance performance, functional and neuromuscular adaptations were quantified by postural sway as well as co-contraction index of antagonistic shank and thigh muscle pairs.
Protocol 1—spinning top (ST).
Subjects had to balance on the left leg on a spinning top (ST; Fig 2A). This test protocol focused on static stability to assess adaptations in a test condition corresponding to the postural strategy of SMT (fixed point at the ankle joint) [7,42–44]. By standing as still as possible on the unstable support surface, subjects had to produce and compensate self-initiated postural control manoeuvres. We paid particular attention that this device was not exercised during the four week SMT intervention.
Protocol 2—swinging platform (SP).
Subjects had to balance on the left leg on a free-swinging platform (SP; Fig 2A). This test protocol focused on the postural requirement profile similar to RBT (fixed point in the proximal body part) [16,17], challenging the subjects to maintain equilibrium on a freely oscillating support surface. This device (Posturomed®, Haider Bioswing, Germany) is frequently used to assess balance performance with high test-retest reproducibility and consists of a platform attached to a solid frame via two steel ropes on each corner [45–47]. Subjects were instructed to stand as still as possible were not exposed to perturbations.
Protocol 3—Transfer task with cognitive interference (CI).
This task was applied to establish whether there is any transfer effect of specificities regarding balance performance using cognitive interference (CI; [39,40,48]). Cognitive interference during postural demanding tasks—frequently occurring in everyday life—is known to comprise performance capacity and is related to an increased fall risk [5,49–51]. Subjects balanced on the left leg on a spinning top while performing a cognitive dual task (Fig 2A). CI was applied by means of simultaneous mental calculation (maths summation task; [39,49,52]). Subjects had to count in steps of seven starting from a number randomly chosen by the operator. Instructions were given to count as quickly and accurately as possible.
Postural sway during ST and CI was quantified by means of the centre of pressure (COP) displacement on a force plate (AMTI, Watertown, USA). 3D ground reaction forces were sampled at 50Hz, and total (COPtotal), anterior-posterior (a-p, COPap) and medial-lateral (m-l, COPml) COP displacement was determined. Sway path of the swinging platform (SP) was assessed by means of a movable goniometer attached to the platform and quantified in a-p and m-l direction. COP and sway path were used to allocate subjects by matched pairs either to the SMT or to the RBT group.
Electromyographic (EMG) activity.
Bipolar Ag/AgCl surface electrodes (Ambu Blue Sensor P, Ballerup, Denmark; diameter 9mm, centre-to-centre distance 25mm) were placed over the soleus (SOL), medial gastrocnemius (GM), tibialis anterior (TA), rectus femoris (RF) and biceps femoris (BF) of the left leg. The longitudinal axes of the electrodes were in line with the presumed direction of the underlying muscle fibres according to SENIAM . The reference electrode was placed on the patella. Interelectrode resistance was kept below 2kΩ by means of shaving, light abrasion and degreasing of the skin with a disinfectant. The EMG signals were transmitted via shielded cables to the amplifier (band-pass filter 10Hz to 1kHz, 1000x amplified) and recorded with 1kHz (A/D-conversion via a National Instruments PCI-6229 DAQ-card, 16bit resolution). Preliminary isometric maximal voluntary contractions (MVC) were performed for all recorded muscles according to Roelants et al.  for normalization. Co-contraction indices (CCIs) were calculated for the antagonistic muscles GM_TA, SOL_TA and RF_BF as the CCI is an indicator for balance ability reflecting the coordination of the task specific muscle activation and hence the functional level of intermuscular coordination [55–57].
30 seconds of COPap and COPml (for ST and CI) and sway path in a-p and m-l direction (for SP) were assessed. Data were averaged for trials and subjects. Post values were normalized to the corresponding values of the pre-test.
For each of the recorded muscles in the three protocols, EMG signals with a length of 30 seconds were rectified, integrated, averaged over the three trials (iEMG [mVs]) and normalized to the individual MVC. Further, to assess the simultaneous activation of antagonistic muscles encompassing the ankle and knee joint as a measure for the ability to adapt intermuscular coordination during balance performance task-specifically [55–57], CCI was calculated with the rectified EMG normalized to the individual MVC by means of the following equation for each antagonistic muscle pair : CCIi = (EMGi of the muscle which was lower activated / EMGi of the muscle which was higher activated) x (EMGi of the muscle which was lower activated + EMGi of the muscle which was higher activated) for each sample point i [0–30.000], CCI = Σ CCIi.
To determine differences in the adaptations between the two groups [RBT-group vs. SMT-group] and the two time points [pre vs. post] a repeated measures analysis of variance (rmANOVA) was conducted for each of the three tasks (ST, SP and CI) for the dependent variables CCI (GM_TA, SOL_TA, RF_BF) and COP (COPap, COPml)/sway path (a-p, m-l), respectively. If the assumption of sphericity measured by Mauchly's sphericity test was violated, Greenhouse-Geisser correction was used. The level of significance was defined at P<0.05. Further, to elucidate possible specificities between the respective training intervention in adaptations of the above mentioned parameters, eta squared (η2) was calculated as an effect size for the pairwise comparisons of the repeated measure factor time (with the interpretation of the size according to Cohen : small: 0.01, medium: 0.06, large: 0.12). To detect training effects for each training group, T-tests were used for pairwise comparisons [pre vs. post] with the level of significance at p<0.05. To correct for multiple testing, we used Bonferroni; each p-value (pi) for each test was multiplied by the number of tests (pi adjusted = pi * n, n = number of tests). If pi adjusted was <0.05, we considered the respective test i to be of statistical significance. Statistical methods were conducted with the statistical software SPSS 20.0 (SPSS, Inc., Chicago, IL, USA).
Grand means of the postural sway and the CCIs are displayed in Table 1 for ST, Table 2 for SP and Table 3 for CI; percentage changes in postural sway and in CCIs in response to both training interventions are illustrated in Fig 2B.
COPap displacement was significantly reduced for both groups in the ST protocol; thereby a greater reduction was observed for the SMT-group (-15%) compared to the RBT-group (-9%). COPml displacement/m-l platform sway was significantly reduced for both groups in all protocols ST, SP and CI: thereby the SMT-group revealed a greater reduction and larger effect sizes in the ST protocol (SMT -18%; RBT -8%) and the RBT-group revealed a greater reduction as well as larger effect sizes in the SP (SMT -22%; RBT -30%) and in the transfer condition CI (SMT -14%; RBT -23%) (Fig 2B). Between group comparison revealed no significant results.
In both groups in all three protocols (ST, SP, CI), CCIs in the muscles encompassing the ankle joint GM_TA (SMT -33%, -22%, -32%; RBT -14%, -41%, -18%) and SOL_TA (SMT -32%, -26%, -39%; RBT -22%, -49%, -20%) were significantly reduced, with greater effect sizes for SMT, respectively. CCIs in RF_BF were significantly reduced in both groups during ST and SP protocols, with large effect sizes for RBT, whereas the SMT group showed very small effect sizes for thigh CCI reduction in both test protocols. Further, a greater reduction was observed for the SMT-group during ST (SMT -36%; RBT -18%), and for the RBT-group during SP (SMT -21%; RBT -45%) (Fig 2B). Moreover, post hoc analyses revealed that the reduction in thigh CCIs (RF_BF) for both SP and the transfer condition CI was only significant in the RBT-group, whereas the SMT-group showed no significant RF_BF reduction in thigh CCI in these two protocols (see Fig 2B). Between group comparisons revealed no significant results.
The purpose of the study was to ascertain adaption specificities in response to the two types of balance training interventions. Our study revealed three main results. 1) Specific stimuli result in distinct adaptations. Although balance performance improved in both intervention groups in all test paradigms, percentage changes and effect sizes differed dependent on the paradigm: When training and paradigm coincided, effects were augmented. 2) These specificities were accompanied by neuromuscular segmental distinctions with a greater emphasis on the proximal body segment in the RBT-group and on the distal segment in the SMT-group. 3) Larger improvements in balance performance with simultaneous cognitive interference were observed after RBT, indicating augmented transfer effects from one specific training paradigm to another multi-task balance setting.
Specificity of adaptations and segmental distinction
Although between group comparisons revealed no significant results, effect sizes and percentages clearly represent distinct influences of the two training interventions which point towards specific adaptations regarding the functional performance and the segmental differentiation of neuromuscular adaptations between both groups. Reductions in sway path and COP displacements were enhanced by 11–36% in the respective paradigm in which postural demands corresponded with the trained balance exercise (Fig 2B). These adaptations were emphasized specifically with a greater reduction for the SMT-group during ST and for the RBT-group during SP and CI. According to literature, this result has functional relevance for both groups: reductions in sway paths are associated with a decreased incidence of ankle injuries  and a reduced risk of falls . Differences appeared in both directions, m-l and a-p. However, percentage changes in the m-l plane of motion are much more pronounced (Tables 1, 2 and 3). This finding seems of considerable relevance, as Lord et al.  have shown that the postural sway in m-l direction displayed a higher correlation with an individual risk of falling.
Moreover, the observed task-specific improvements in functional balance performance are accompanied by a reduced co-contraction of antagonistic muscles. Both intervention groups showed diminished co-contraction of antagonistic muscle pairs after training. As shown by the effect sizes, reductions in contraction indices were pronounced to different extents: regardless of the amount of reduction, for SMT, larger effects of the diminished simultaneously activated antagonistic muscles appear in the distal muscles encompassing the ankle joint, whereas vice versa for RBT effects of diminished co-contractions are more pronounced for the proximal muscles stabilizing the knee and hip joint. This segmental distinction could be observed independent of the test-paradigm (ST or SP). According to previous studies [61,63,55], a high muscle co-contraction reflected by simultaneously activated antagonistic muscle groups points towards a rigid articular stiffening of posture, leading to a general mechanical fixation of that specific limb. Due to this kind of joint stiffening, the ability to react precisely and to rapidly modify movement strategies is restricted, which in turn may lead to greater postural sway [55,64]. Thus, a lower co-contraction is associated with better postural control ability. It is assumed that balance training positively affects the task specific muscle activation which consequently results in an optimized intermuscular coordination [56,57].
Regarding the segmental distinction of neuromuscular adaptations, the training specific effects might be based upon the fact that the two training regimens require—at least in part—different motor control strategies to maintain postural stability. Aspects dealing with the biomechanical differences of the training modalities may be substantial for the interpretation of the results: In both modalities, the controlled variable is the COM , but vertical stabilization of the COM vector above the ankle joint is achieved differently for SMT compared to RBT. With the focus to stand as still as possible, a typical situation in SMT, the human body mainly acts as a single inverted pendulum. Biomechanically, this type of motor control requires a large torque in the ankle joint, mainly produced by muscles encompassing the distal segment [9,20,44]. In contrast, experiments executed in perturbed upright stance revealed that the proximal segment moves into focus to relocate the COM back to the vertical (Fig 1) [10,16,27]. It is supposed that—in contrast to the distal control during SMT—the control of the trunk is the fundamental strategy to keep equilibrium after perturbation [23,24,65] and stabilizing joint torques are distributed from the ankle towards the knee and hip joints [16,24,35,36].
Consequently, different muscle activation patterns are needed when comparing control of static posture during unperturbed stance and control of static posture while perturbations of the support surface are applied [18,19]: during SMT, when standing as still as possible, balance control is supposed to be predominantly based on proprioceptive sensory input via the Ia afferent pathway evoking a mainly reflex based muscle activation within the shank muscles [7,9,16,34]. As a consequence, and as previously shown in a number of studies, neuromuscular adaptations in response to SMT predominantly occur in distal muscles [6,66], reflected by the reduced co-contraction of antagonistic shank muscles in our results. In contrast, when postural control is challenged by external stimulation (i.e. perturbations of the support surface), it is supposed that proximal muscle activity (i.e. thigh muscles) is associated with the control of trunk orientation to restore equilibrium on the perturbed platform [16,27,28,67,68] and it is assumed that corticospinal pathways via polysynaptic II afferents are involved in the neuromuscular control of postural responses [69–71]. Thereby, thigh and hip muscles are activated to compensate for the higher torques produced by external perturbation by generating appropriate compensatory torques in the knee and hip joints [17,28,35]. As a consequence, as shown in our study for the first time, RBT emphasized neuromuscular adaptations in the proximal leg segment, reflected by a reduced co-contraction of antagonistic thigh muscles.
“Multi-tasking” is commonly required to perform a wide spectrum of daily activities . Interestingly, the RBT-group revealed 64 percent greater improvements than the SMT-group in balance performance—especially in m-l direction—when simultaneously interfered with cognitive demands. This finding indicates that transfer effects into dual task settings with CI are greater for RBT than for SMT. CI—identified as a major fall risk factor—is highly relevant for fall prevention [38,73]: restrictions in simultaneous cognitive processing and muscle coordination are interrelated with postural instability and increased incidence of falls [29,74]. Training regimens that counteract these deficits in complex multitask settings are highly applicable for subpopulations suffering from an enhanced risk of fall-induced injuries.
In view of literature [38–40,73], until now, balance performance during CI could only be improved in response to CI training; no effects have been observed for balance training executed without CI. Thus our findings are surprising. We can just speculate about the underlying mechanisms: one major factor could be the different motor control strategies within both training interventions as mentioned above. Whereas during SMT it is supposed that postural control is mainly attributed to subcortical centres and reflex activity [34,66,75–77], there is evidence that during RBT the postural responses could be seen as a particular kind of voluntary movement, which is thought to be under control of the motor cortex and hence under a larger influence of cortical areas suggesting an involvement of transcortical loops [77–82]. In particular, it can be assumed that in addition to spinal pathways during the initial part of the muscular response, within the late reflex component (after 85ms) direct corticospinal pathways contribute to the neuromuscular control of perturbed stance [77,78,80,82]. Based on this, it can be speculated that a balance training which includes the usage of corticospinal pathways—as it holds true for RBT—may result in an improvement of the processing of such circuits. Hence, this improvement may have led to a better capacity for additional cognitive demands—and hence to the better functional improvement within the RBT group. Considering other factors contributing to the larger transfer effect within the RBT-group, we assume that variability and segmental strategy also play a role. First, results from Rhea et al.  and Yao et al.  indicate that the more variable and complex a stimulus is, the more postural control systems are challenged and the greater is the spectrum of trained manners. As the variability is higher during RBT by applying random surface perturbations varying in direction, amplitude, pause and perturbation length, we assume that the ability to effectively transfer performance gains from the frequently repeated task led to enhanced postural stability in CI. Secondly, neuromuscular control of the proximal segment may also have influenced balance performance positively during CI. An improved muscle synergy accompanied by diminished antagonistic co-contraction in the thigh muscles is associated with an enhanced COM control  and thus may have led to an improved balance performance.
Although training settings have been matched for RBT and SMT in terms of duration, frequency and rest interval of training periods and sessions, we cannot exclude possible differences in training load and intensity. Thus, this needs to be mentioned as a limitation of the study.
Our findings elucidate that adaptations in postural control are multi-segmental and functionally specific, depending on the postural strategy which may predominate to control body COM during training. The specificity of training modalities—all combined under the term “balance training”—shows that it is important to adequately distinguish cause and effect between the respective types of balance interventions. Regarding possible implications, commonly SMT has been described as being beneficial in general to rehabilitate from ankle injuries  and to prevent postural deficits [7,85]. Hence, with the focus on the ankle prevention and rehabilitation or chronic ankle instabilities, SMT serves as an adequate postural training intervention . Based on the current findings, RBT could serve as a further expansion to include the proximal segment, and thus the control of structures near to the body’s COM, into training. For instance, RBT could promote the prevention and rehabilitation in athletes and other subpopulations suffering from knee and thigh injuries. Concerning fall prevention, the strategy to precisely control upper body segment oscillations is assumed to contribute to the risk of falling [25,87]. Further, considering fall or injury mechanisms, it can be assumed that RBT addresses anticipatory postural skills more than SMT. Together with the higher ability to transfer performance after RBT, this seems promising: in particular, for risk populations such as older people or patients with neurological deficits such as Parkinson or Multiple Sclerosis, the training of postural corrective responses which occur in typical high fall risk situations might be useful. To conclude, it is suggested to adjust the choice of the adequate training intervention to the specific target group (i.e. for patients, athletes, older people), and to particularly identify the aim of the intervention and which structures want to be addressed, to then involve the specific postural strategy within the training. If no specific aim exists, we recommend using both SMT and RBT in expansion to each other.
The authors want to thank the DLR Spaceflight Department and particularly Dr. Hans-Ulrich Hoffmann for the support.
- Conceptualization: KF AK AG RR.
- Data curation: KF AK AG RR.
- Formal analysis: KF AK AG RR.
- Funding acquisition: KF AG RR.
- Investigation: KF AK AG RR.
- Methodology: KF AK AG RR.
- Project administration: KF AK AG RR.
- Resources: KF AK AG RR.
- Supervision: AG RR.
- Validation: KF AK AG RR.
- Visualization: KF AK AG RR.
- Writing – original draft: KF AK AG RR.
- Writing – review & editing: KF AK AG RR.
- 1. Silva P, Figueredo Borges Botelho PF, de Oliveira Guirro EC, Vaz MM, de Abreu DC. Long-term benefits of somatosensory training to improve balance of elderly with diabetes mellitus. J Bodyw Mov Ther. 2015; 19(3): 453–457. pmid:26118517
- 2. Madureira MM, Takayama L, Gallinaro AL, Caparbo VF, Costa RA, Pereira RMR. Balance training program is highly effective in improving functional status and reducing the risk of falls in elderly women with osteoporosis: a randomized controlled trial. Osteoporosis Int. 2007; 18(4): 419–425.
- 3. Overstall PW. The use of balance training in elderly people with falls. Rev Clin Gerontol. 1999; 13(2): 153–161.
- 4. Pan X & Bai J. Balance training in the intervention of fall risk in elderly with diabetic peripheral neuropathy: A review. Int J Nursing Sci. 2014; 1(4): 441–445.
- 5. Granacher U, Muehlbauer T, Gollhofer A, Kressig RW, Zahner L. An intergenerational approach in the promotion of balance and strength for fall prevention—a mini-review. Gerontology. 2011; 57(4): 304–315. pmid:20720401
- 6. Rozzi SL, Lephart SM, Sterner R, Kuligowski L. Balance training for persons with functionally unstable ankles. J Orthop Sports Phys Ther. 1999; 29(8): 478–486. pmid:10444738
- 7. Taube W, Gruber M, Gollhofer A. Spinal and supraspinal adaptations associated with balance training and their functional relevance. Acta physiol. 2008; 193(2): 101–116.
- 8. Lesinski M, Hortobagyi T, Muehlbauer T, Gollhofer A, Granacher U. Effects of Balance Training on Balance Performance in Healthy Older Adults: A Systematic Review and Meta-analysis. Sport med. 2015; 45(12): 1721–1738.
- 9. Winter DA, Patla AE, Prince F, Ishac M, Gielo-Perczak K. Stiffness control of balance in quiet standing. J Neurophysiol. 1998; 80(3): 1211–1221. pmid:9744933
- 10. Gage WH, Winter DA, Frank JS, Adkin AL. Kinematic and kinetic validity of the inverted pendulum model in quiet standing. Gait Posture. 2004; 19(2): 124–132. pmid:15013500
- 11. Maurer C & Peterka RJ. A new interpretation of spontaneous sway measures based on a simple model of human postural control. J Neurophysiol. 2005; 93(1): 189–200. pmid:15331614
- 12. Maurer C, Mergner T, Peterka RJ. Multisensory control of human upright stance. Exp Brain Res. 2006; 171(2): 231–250. pmid:16307252
- 13. Nashner LM & McCollum G. The organization of human postural movements: A formal basis and experimental synthesis. Behav Brain Sci. 1985(8): 135–172.
- 14. Mansfield A, Aqui A, Centen A, Danells CJ, DePaul VG, Knorr Set al. Perturbation training to promote safe independent mobility post-stroke: study protocol for a randomized controlled trial. BMC neurology. 2015; 15:87.
- 15. Gruneberg C, Bloem BR, Honegger F, Allum JHJ. The influence of artificially increased hip and trunk stiffness on balance control in man. Exp Brain Res. 2004; 157(4): 472–485. pmid:15138751
- 16. Horak FB & Nashner LM. Central programming of postural movements: adaptation to altered support-surface configurations. J Neurophysiol. 1986; 55(6): 1369–1381. pmid:3734861
- 17. Horak FB & Macpherson JM1996. Postural Orientation and Equilibrium. Rowell L. B., & Sheperd J. T.(Eds.), Handbook of Physiology, Section 12. Oxford University Press: New York.
- 18. Giboin L, Gruber M, Kramer A. Task-specificity of balance training. Hum Movement Sci. 2015; 44:22–31.
- 19. Muehlbauer T, Besemer C, Wehrle A, Gollhofer A, Granacher U. Relationship between strength, power and balance performance in seniors. Gerontology. 2012; 58(6): 504–512. pmid:22922168
- 20. Winter DA, Patla AE, Ishac M, Gage WH. Motor mechanisms of balance during quiet standing. J Electromyogr Kines. 2003; 13(1): 49–56.
- 21. Boyas S, Remaud A, Bisson EJ, Cadieux S, Morel B, Bilodeau M. Impairment in postural control is greater when ankle plantarflexors and dorsiflexors are fatigued simultaneously than when fatigued separately. Gait Posture. 2011; 34(2): 254–259. pmid:21646020
- 22. Gatev P, Thomas S, Kepple T, Hallett M. Feedforward ankle strategy of balance during quiet stance in adults. J Physiol. 1999; 514(3): 915–928.
- 23. Buchanan JJ & Horak FB. Emergence of postural patterns as a function of vision and translation frequency. J Neurophysiol 1999; 81(5): 2325–2339. pmid:10322069
- 24. Chen C, Lou S, Wu H, Wu S, Yeung K, Su F. Effects of the type and direction of support surface perturbation on postural responses. J Neuroeng Rehabil. 2014; 11:50. pmid:24708582
- 25. Bobrova EV, Levik YS, Bogacheva IN. Oscillations of upper and lower body segments in the sagittal plane during standing. Biophysics. 2009; 54(5): 648–651.
- 26. Hughes MA, Schenkman ML, Chandler JM, Studenski SA. Postural responses to platform perturbation: kinematics and electromyography. Clin Biomech. 1995; 10(6): 318–322.
- 27. Dietz V, Trippel M, Ibrahim IK, Berger W. Human stance on a sinusoidally translating platform: balance control by feedforward and feedback mechanisms. Exp Brain Res. 1993; 93(2): 352–362. pmid:8491275
- 28. Kuo AD & Zajac FE. Human standing posture: multi-joint movement strategies based on biomechanical constraints. Prog Brain Res. 1993; 97:349–358. pmid:8234760
- 29. Horak FB. Postural orientation and equilibrium: what do we need to know about neural control of balance to prevent falls? Age Ageing. 2006; 35 Suppl 2:ii7–ii11.
- 30. McIlroy WE & Maki BE. Age-related changes in compensatory stepping in response to unpredictable perturbations. The journals of gerontology. Series A, Biological sciences and medical sciences. 1996; 51(6): M289–96.
- 31. Mansfield A & Maki BE. Are age-related impairments in change-in-support balance reactions dependent on the method of balance perturbation? J Biomech. 2009; 42(8): 1023–1031. pmid:19362311
- 32. Bieryla KA & Madigan ML. Proof of concept for perturbation-based balance training in older adults at a high risk for falls. Arch Phys Med Rehab. 2011; 92(5): 841–843.
- 33. Shumway-Cook A, Hutchinson S, Kartin D, Price R, Woollacott M. Effect of balance training on recovery of stability in children with cerebral palsy. Dev Med Child Neurol. 2003; 45(9): 591–602. pmid:12948326
- 34. Nashner LM. Adapting reflexes controlling the human posture. Exp Brain Res. 1976; 26(1): 59–72. pmid:964327
- 35. Ge W. Age-related differences in body segmental movement during perturbed stance in humans. Clin Biomech (Bristol, Avon). 1998; 13(4–5): 300–307.
- 36. Henry SM, Fung J, Horak FB. EMG responses to maintain stance during multidirectional surface translations. J Neurophysiol. 1998; 80(4): 1939–1950. pmid:9772251
- 37. Resch JE, May B, Tomporowski PD, Ferrara MS. Balance performance with a cognitive task: a continuation of the dual-task testing paradigm. J Athl Training. 2011; 46(2): 170–175.
- 38. Silsupadol P, Siu K, Shumway-Cook A, Woollacott MH. Training of balance under single- and dual-task conditions in older adults with balance impairment. Phys Ther. 2006; 86(2): 269–281. pmid:16445340
- 39. Granacher U, Wolf I, Wehrle A, Bridenbaugh S, Kressig RW. Effects of muscle fatigue on gait characteristics under single and dual-task conditions in young and older adults. J Neuroeng Rehabil. 2010; 7:56. pmid:21062458
- 40. Granacher U, Muehlbauer T, Bridenbaugh S, Bleiker E, Wehrle A, Kressig RW. Balance training and multi-task performance in seniors. Int J Sport Med. 2010; 31(5): 353–358.
- 41. Freyler K, Gollhofer A, Colin R, Brüderlin U, Ritzmann R. Reactive Balance Control in Response to Perturbation in Unilateral Stance. PLoS one. 2015; 10(12): e0144529. pmid:26678061
- 42. Emery CA, Cassidy JD, Klassen TP, Rosychuk RJ, Rowe BH. Effectiveness of a home-based balance-training program in reducing sports-related injuries among healthy adolescents: a cluster randomized controlled trial. Can Med Assoc J. 2005; 172(6): 749–754.
- 43. Hoffman M & Payne VG. The effects of proprioceptive ankle disk training on healthy subjects. The Journal of orthopaedic and sports physical therapy. 1995; 21(2): 90–93. pmid:7711762
- 44. Peterka RJ. Sensorimotor integration in human postural control. J Neurophysiol. 2002; 88(3): 1097–1118. pmid:12205132
- 45. Boeer J, Mueller O, Krauss I, Haupt G, Axmann D, Horstmann T. Effects of a sensory-motor exercise program for older adults with osteoarthritis or prosthesis of the hip using measurements made by the Posturomed oscillatory platform. J Geriatr Phys Ther. (2001). 2010; 33(1): 10–15.
- 46. Boeer J, Mueller O, Krauss I, Haupt G, Horstmann T. Zuverlässigkeitsprüfung eines Messverfahrens zur Charakterisierung des Standverhaltens und Quantifizierung des Balancevermögens auf einer instabilen Plattform (Posturomed). Sportverletz Sportschaden. 2010; 24(01): 40–45.
- 47. Müller O, Günther M, Krauss I, Horstmann T. Physikalische Charakterisierung des Therapiegerätes Posturomed als Messgerät—Vorstellung eines Verfahrens zur Quantifizierung des Balancevermögens. Biomedizinische Technik. Biomedical engineering. 2004; 49(3): 56–60.
- 48. Granacher U, Muehlbauer T, Gruber M. A qualitative review of balance and strength performance in healthy older adults: impact for testing and training. J Aging Res. 2012; 2012:708905.
- 49. Rankin JK, Woollacott MH, Shumway-Cook A, Brown LA. Cognitive influence on postural stability: a neuromuscular analysis in young and older adults. The journals of gerontology. Series A, Biological sciences and medical sciences. 2000; 55(3): M112–9.
- 50. Granacher U, Muehlbauer T, Gollhofer A, Kressig RW, Zahner L. Evidence-based and evidence-inspired: an intergenerational approach in the promotion of balance and strength for fall prevention. Gerontology. 2011; 57(5): 424–426. pmid:21196693
- 51. Brauer SG, Broome A, Stone C, Clewett S, Herzig P. Simplest tasks have greatest dual task interference with balance in brain injured adults. Hum Movement Sci. 2004; 23(3–4): 489–502.
- 52. Beauchet O, Dubost V, Herrmann FR, Kressig RW. Stride-to-stride variability while backward counting among healthy young adults. J Neuroeng Rehabil. 2005; 2:26. pmid:16095533
- 53. Hermens HJ, Freriks B, Disselhorst-Klug C, Rau G. Development of recommendations for SEMG sensors and sensor placement procedures. J Electromyogr Kines. 2000; 10(5): 361–374.
- 54. Roelants M, Verschueren SMP, Delecluse C, Levin O, Stijnen V. Whole-body-vibration-induced increase in leg muscle activity during different squat exercises. J Strength Cond Res. 2006; 20(1): 124–129. pmid:16503671
- 55. Tucker MG, Kavanagh JJ, Barrett RS, Morrison S. Age-related differences in postural reaction time and coordination during voluntary sway movements. Hum Movement Sci. 2008; 27(5): 728–737.
- 56. Nagai K, Yamada M, Uemura K, Yamada Y, Ichihashi N, Tsuboyama T. Differences in muscle coactivation during postural control between healthy older and young adults. Arch Gerontol Geriat. 2011; 53(3): 338–343.
- 57. Bruhn S, Kullmann N, Gollhofer A. The effects of a sensorimotor training and a strength training on postural stabilisation, maximum isometric contraction and jump performance. Int J Sport Med. 2004; 25(1): 56–60.
- 58. Lewek MD, Rudolph KS, Snyder-Mackler L. Control of frontal plane knee laxity during gait in patients with medial compartment knee osteoarthritis. Osteoarthr Cartilage. 2004; 12(9): 745–751.
- 59. Cohen J1988. Statistical power analysis for the behavioral sciences (2nd ed.). Lawrence Erlbaum: New Jersey.
- 60. Melzer I & Oddsson LI. Improving balance control and self-reported lower extremity function in community-dwelling older adults: a randomized control trial. Clin Rehabil. 2013; 27(3): 195–206. pmid:22837541
- 61. Nagai K, Yamada M, Tanaka B, Uemura K, Mori S, Aoyama Tet al. Effects of balance training on muscle coactivation during postural control in older adults: a randomized controlled trial. The journals of gerontology. Series A, Biological sciences and medical sciences. 2012; 67(8): 882–889. pmid:22389467
- 62. Lord SR, Rogers MW, Howland A, Fitzpatrick R. Lateral stability, sensorimotor function and falls in older people. Am Geriatr Soc. 1999; 47(9): 1077–1081.
- 63. Nagai K, Yamada M, Mori S, Tanaka B, Uemura K, Aoyama Tet al. Effect of the muscle coactivation during quiet standing on dynamic postural control in older adults. Arch Gerontol Geriatr. 2013; 56(1): 129–133. pmid:22959815
- 64. Allum JHJ, Carpenter MG, Honegger F, Adkin AL, Bloem BR. Age-dependent variations in the directional sensitivity of balance corrections and compensatory arm movements in man. J Physiol. 2002; 542(2): 643–663.
- 65. Ferber R, Osternig LR, Woollacott MH, Wasielewski NJ, Lee J. Reactive balance adjustments to unexpected perturbations during human walking. Gait Posture. 2002; 16(3): 238–248. pmid:12443948
- 66. Taube W, Kullmann N, Leukel C, Kurz O, Amtage F, Gollhofer A. Differential reflex adaptations following sensorimotor and strength training in young elite athletes. Int J Sport Med. 2007; 28(12): 999–1005.
- 67. Horstmann GA & Dietz V. A basic posture control mechanism: the stabilization of the centre of gravity. Electroen Clin Neuro. 1990; 76(2): 165–176.
- 68. McCollum G & Leen TK. Form and exploration of mechanical stability limits in erect stance. J Motor Behav. 1989; 21(3): 225–244.
- 69. Dietz V, Horstmann G, Berger W. Involvement of different receptors in the regulation of human posture. Neurosci Lett. 1988; 82(87): 82–87.
- 70. Gollhofer A, Horstmann G, Berger W, Dietz V. Compensation of translational and rotational perturbations in human posture: stabilization of the centre of gravity. Neurosci Lett. 1989; 105: 73–78. pmid:2485889
- 71. Gottlieb GL, Agarwal GC, Jaeger RJ. Response to Sudden Torques About Ankle in Man. IV. A Functional Role of a-y Linkage. J Neurophysiol. 1981; 46(1): 179–190. pmid:7264709
- 72. Gschwind YJ, Kressig RW, Lacroix A, Muehlbauer T, Pfenninger B, Granacher U. A best practice fall prevention exercise program to improve balance, strength / power, and psychosocial health in older adults: study protocol for a randomized controlled trial. BMC geriatrics. 2013; 13:105. pmid:24106864
- 73. Halvarsson A, Franzen E, Stahle A. Balance training with multi-task exercises improves fall-related self-efficacy, gait, balance performance and physical function in older adults with osteoporosis: a randomized controlled trial. Clin Rehabil. 2015; 29(4): 365–375. pmid:25142277
- 74. Jacobs JV, Nutt JG, Carlson-Kuhta P, Allen R, Horak FB. Dual tasking during postural stepping responses increases falls but not freezing in people with Parkinson's disease. Parkinsonism Relat D. 2014; 20(7): 779–781.
- 75. Gruber M, Gruber SBH, Taube W, Schubert M, Beck SC, Gollhofer A. Differential effects of ballistic versus sensorimotor training on rate of force development and neural activation in humans. J Strength Cond Res. 2007; 21(1): 274–282. pmid:17313292
- 76. Taube W, Gruber M, Beck S, Faist M, Gollhofer A, Schubert M. Cortical and spinal adaptations induced by balance training. Acta Physiol. 2007; 189(4): 347–358.
- 77. Keck ME, Pijnappels M, Schubert M, Colombo G, Curt A, Dietz V. Stumbling reactions in man: influence of corticospinal input. Electroencephalogr Clin Neurophysiol. 1998; 3(109): 215–223.
- 78. Taube W, Schubert M, Gruber M, Beck S, Faist M, Gollhofer A. Direct corticospinal pathways contribute to neuromuscular control of perturbed stance. J Appl Physiol. 2006; 101(2): 420–429. pmid:16601305
- 79. Jacobs JV & Horak FB. Cortical control of postural responses. J Neural Transm. 2007; 114(10): 1339–1348. pmid:17393068
- 80. Solopova IA, Kazennikov OV, Deniskina NB, Levik YS, Ivanenko YP. Postural instability enhances motor responses to transcranial magnetic stimulation in humans. Neurosci Lett. 2003; 337(1): 25–28. pmid:12524163
- 81. Maki BE & McIlroy WE. Cognitive demands and cortical control of human balance-recovery reactions. J Neural Transm. 2007; 114(10): 1279–1296. pmid:17557125
- 82. Lavoie BA, Cody FW, Capaday C. Cortical control of human soleus muscle during volitional and postural activities studied using focal magnetic stimulation. Exp Brain Res. 1995; 103(1): 97–107. pmid:7615042
- 83. Rhea CK, Wutzke CJ, Lewek MD. Gait dynamics following variable and constant speed gait training in individuals with chronic stroke. Gait Posture. 2012; 36(2): 332–334. pmid:22503594
- 84. Yao WX, Cordova A, de Sola W, Hart C, Yan AF. The effect of variable practice on wheelchair propulsive efficiency and propulsive timing. Euro J Phys Rehab Med. 2012; 48(2): 209–216.
- 85. Swartz EE & Bruce LA. Balance Training for Neuromuscular Control and Performance Enhancement. Athletic Training & Sports Health Care. 2011; 3(4): 171–173.
- 86. McKeon PO & Hertel J. Systematic review of postural control and lateral ankle instability, part II: is balance training clinically effective? J Athl Train. 2008; 43(3): 305–315. pmid:18523567
- 87. Pai YC & Patton J. Center of mass velocity-position predictions for balance control. J Biomech. 1997; 30(4): 347–354. pmid:9075002