- Original article
- Open Access
Adaptation effects in static postural control by providing simultaneous visual feedback of center of pressure and center of gravity
© The Author(s). 2017
- Received: 20 December 2016
- Accepted: 4 July 2017
- Published: 19 July 2017
The benefit of visual feedback of the center of pressure (COP) on quiet standing is still debatable. This study aimed to investigate the adaptation effects of visual feedback training using both the COP and center of gravity (COG) during quiet standing.
Thirty-four healthy young adults were divided into three groups randomly (COP + COG, COP, and control groups). A force plate was used to calculate the coordinates of the COP in the anteroposterior (COPAP) and mediolateral (COPML) directions. A motion analysis system was used to calculate the coordinates of the center of mass (COM) in both directions (COMAP and COMML). The coordinates of the COG in the AP direction (COGAP) were obtained from the force plate signals. Augmented visual feedback was presented on a screen in the form of fluctuation circles in the vertical direction that moved upward as the COPAP and/or COGAP moved forward and vice versa. The COP + COG group received the real-time COPAP and COGAP feedback simultaneously, whereas the COP group received the real-time COPAP feedback only. The control group received no visual feedback. In the training session, the COP + COG group was required to maintain an even distance between the COPAP and COGAP and reduce the COGAP fluctuation, whereas the COP group was required to reduce the COPAP fluctuation while standing on a foam pad. In test sessions, participants were instructed to keep their standing posture as quiet as possible on the foam pad before (pre-session) and after (post-session) the training sessions.
In the post-session, the velocity and root mean square of COMAP in the COP + COG group were lower than those in the control group. In addition, the absolute value of the sum of the COP − COM distances in the COP + COG group was lower than that in the COP group. Furthermore, positive correlations were found between the COMAP velocity and COP − COM parameters.
The results suggest that the novel visual feedback training that incorporates the COPAP–COGAP interaction reduces postural sway better than the training using the COPAP alone during quiet standing. That is, even COPAP fluctuation around the COGAP would be effective in reducing the COMAP velocity.
- Center of gravity
- Center of mass
- Center of pressure
- Static posture
- Visual feedback training
The ability to maintain balance in static postures relies on the ability of the central nervous system to control movements or positional fluctuations by using the body’s center of mass (COM) so that it remains within safe boundaries above the base of support [1, 2]. If static balance during quiet standing is controlled by shifting the center of pressure (COP) through the feet, the body will move as a single segment, often modeled as an inverted pendulum . Previous studies have reported that the augmented visual feedback of the COP has been used for static balance training [4–6].
However, the benefits gained from visual feedback of the COP during quiet standing are still under debate [7, 8]. Kilby et al. reported that the real-time visual feedback of neither the COP nor the COM affected the postural motion of healthy adults during quiet standing ; in other words, neither the COP nor the COM velocities changed when conditions were altered between a presence and lack of augmented visual feedback. In addition, the participants in the study of Lakhani et al. showed no postural stability learning effects when visual feedback training was using either as a vertical projection of the COM onto the ground (i.e., the center of gravity (COG)) or the COP during quiet standing . In fact, under no feedback conditions did the root mean square values of the COP or COG change between the pre-training and post-training sessions.
The impact of the difference in position between the COP and COG (COP–COG distance) on postural stability in static balance has also been investigated . A larger COP–COG distance has been shown to indicate greater body acceleration during quiet standing [12, 13]. During quiet standing, the COP–COG distance increases with age and depends on whether the participant’s eyes are closed or open [12, 14]. Postural instability may result from biased positioning of the COP relative to the COG, as this will result in a unidirectional moment acting on the COM . In fact, Mani et al. reported that elderly participants were not able to maintain equilibrium standing on one leg when the position of the COP was biased relative to the COG, such as when the COP was located laterally in the direction of the supporting leg, while the younger group of participants experienced less difficulty . In addition, Ibuki et al. reported that the COP − COM distance decreased and the COP fluctuated more evenly around the COM during one-legged standing in the ballet dancer group than in the control group . These findings imply that feedback training incorporating the interaction between the COP and COG may be more effective for improving static balance than training using the COP or COG alone.
With this background in mind, the purpose of this study was to investigate the adaptive effects of augmented visual feedback training using both the COP and COG, as compared to training using only the COP, during quiet standing. The hypothesis was that novel balance training, which incorporates the interaction between the COP and COG using simultaneously the visual feedback of both, would reduce postural sway compared to training that used the COP alone without feedback. The findings of this study could contribute toward the development of an effective visual feedback training system for improving postural static balance.
The characteristics of the COP, COP + COG, and control groups
COP (n = 11)
COP + COG (n = 12)
Control (n = 11)
23.2 ± 2.3
22.8 ± 1.6
22.3 ± 2.4
Male 6, female 5
Male 8, female 4
Male 5, female 6
165.7 ± 6.9
169.2 ± 7.6
164.5 ± 8.3
Body weight (kg)
56.8 ± 7.5
59.7 ± 9.0
57.0 ± 9.2
Foot length (cm)
24.2 ± 1.8
24.5 ± 1.6
23.2 ± 1.7
Kinematic data were collected using a six-camera 3D motion analysis system (Motion Analysis Corporation, Santa Rosa, CA, USA) at a sampling frequency of 200 Hz. Twenty reflective markers were attached to the following bony landmarks: the acromioclavicular joint, the lateral epicondyle of the upper arm, the wrist, the head of the second metacarpal, the great trochanter of the femur, the lateral malleolus, the second metatarsal head, the calcaneus, and the C7, S1, and bilateral point of the external acoustic foramen. These markers were used to calculate the COM in the anteroposterior (AP) and mediolateral (ML) directions (COMAP and COMML), based on the 14 body segments and an anthropometrical model . A force plate (Kistler, Winterthur, Switzerland) was used to calculate the coordinates of the COP in the AP (COPAP; Appendix 1) and ML (COPML) directions. Force plate signals were collected at a sampling frequency of 1000 Hz and synchronized with the motion analysis system. The real-time COG in the AP direction (COGAP) was obtained from the force plate signals (Appendix 2) [10, 12].
Augmented visual feedback was provided in the form of fluctuating circles moving vertically upward as the COPAP and COGAP moved forward and downward as they moved backward. LabVIEW software (National Instruments, USA) was used to present this feedback on a screen (height 1.8 m, width 2.5 m) located approximately 5 m away from the participant. The vertical movement of the circles on the screen was 16 times greater than the true COPAP and COGAP displacements .
The participants stood with both their feet placed on a foam pad (thickness 6.5 cm, SAKAI Medical, Japan) throughout the pre-training, training, and post-training sessions. Only the AP direction was applied to reduce feedback complexity and allow the participants to focus on minimizing COP and COG fluctuations along a single axis . The distance of the two horizontal lines on the screen corresponded to the two standard deviations (SD) of the first COGAP displacement measurement. The center point between the two lines identified the center of the force plate in the AP direction.
The participants were instructed to stand barefoot with their arms across their chest in front of a visual target located at an eye-level height on the screen. First, to measure the SD of the COGAP displacements, each participant was instructed to stand quietly with both feet placed together on the force plate with their eyes open for 10 s. Horizontal lines, indicating the two SDs of each participant, were also projected on the screen during the training session (Fig. 1). Subsequently, the participants were required to stand on the foam pad, which was attached to the force plate with double-sided adhesive tapes, as steadily as possible with their feet placed together. The position of the feet on the pad was standardized: the center of the force plate in the sagittal plane was matched with the position of the feet 40% down the length from the heel . The exact location where the feet were to be placed was marked on the pad to ensure that all the participants started with the same foot position in each trial. Each participant was asked to perform 12 trials with a 5-min rest after the first six trials. The break between trials was approximately 1 min, while the time between the trials and pre- or post-sessions was 5 min.
Data and statistical analysis
where N is the total sampling number. Thus, a lower value of COP − COMclose indicated that movements of the COP were held closer to the COM in the AP direction. A shorter COP − COMeven indicated that the COP position was more even, with fewer fluctuations around the COM in the AP direction. All parameters were normalized by the foot length (FL) of each participant.
Both one-way and two-way mixed-design ANOVA were used in each group (factor Group: COP, COP + COG, and control); one-way ANOVA was used to identify and analyze differences in biomechanical characteristics, and two-way mixed-design ANOVA compared the group data to test sessions (factor Test Session: pre and post) to analyze possible differences in the value of the indices. A post hoc analysis was performed using Bonferroni pairwise comparison, and Pearson’s correlation coefficient was used to identify and analyze correlations between the COMAP velocity and COP − COM parameters. The statistical significance was set to p < 0.05 for all tests.
No significant differences were observed among the three groups in terms of age (F 2, 31 = 0.500, p = 0.611), height (F 2, 31 = 1.170, p = 0.324), weight (F 2, 31 = 0.391, p = 0.680), and foot length (F 2, 31 = 1.779, p = 0.186) (Table 1).
The results of postural stability
COP + COG
COMAP velocity (%FL/s)
2.91 ± 0.52*
2.27 ± 0.41†
2.94 ± 0.58
2.74 ± 0.66
3.02 ± 0.41*
2.61 ± 0.34
COMAP RMS (%FL)
3.24 ± 0.72
2.92 ± 0.86†
3.38 ± 1.21
2.86 ± 0.62
3.80 ± 1.09
4.01 ± 1.25
COPAP velocity (%FL/s)
8.40 ± 2.06
8.39 ± 1.52
9.26 ± 2.97
9.07 ± 3.57
8.95 ± 1.66
7.86 ± 1.75
COPAP RMS (%FL)
3.96 ± 0.73
3.54 ± 0.78
4.12 ± 1.13
3.54 ± 0.64
4.33 ± 0.95
4.33 ± 1.12
COMML velocity (%FL/s)
2.99 ± 0.52
2.76 ± 0.34
3.40 ± 0.41*
3.12 ± 0.59
3.10 ± 0.70
2.78 ± 0.38
COMML RMS (%FL)
2.54 ± 0.44
2.59 ± 0.49
2.54 ± 0.40*
3.11 ± 0.67
2.27 ± 0.38
2.59 ± 0.60
COPML velocity (%FL/s)
9.12 ± 2.51
7.99 ± 1.24
10.48 ± 3.02*
8.85 ± 2.72
9.48 ± 2.59
8.63 ± 1.85
COPML RMS (%FL)
3.43 ± 0.47
3.33 ± 0.46
3.61 ± 0.44
3.81 ± 0.74
3.25 ± 0.54
3.29 ± 0.60
No significant effect was observed on the COMAP velocity between Group factors (F 2, 31 = 0.946, p = 0.399). However, the COMAP velocity showed a significant change between Test session factors (F 1, 31 = 42.361, p < 0.001). A significant interaction was observed between the Group and Test session factors in terms of the COMAP velocity (F 2, 31 = 3.391, p = 0.047). The post hoc test revealed that post-session COMAP velocity values were significantly lower in the COP + COG group compared to those in the control group (p = 0.047). For both the COP + COG and control groups, the COMAP velocity in the post-session was significantly lower than that in the pre-session (p < 0.001); however, no significant difference was observed in the COP group between the pre- and post-sessions (p = 0.117).
In terms of COMAP RMS, no significant main effect was observed for the factor Test session (F 1, 31 = 0.979, p = 0.330), nor was there a significant interaction (F 2, 31 = 1.036, p = 0.367). On the other hand, the COMAP RMS showed a significant main effect for the factor Group (F 2, 31 = 4.158, p = 0.025). The post hoc test revealed that the overall COMAP RMS of the COP + COG group was significantly lower than that of the control group (p = 0.042), while there was no significant difference between that of the COP and control groups (p = 0.068). The post-session COMAP RMS of the COP + COG group was significantly lower than that of the control group (p = 0.022); however, there was no significant difference in the pre-session (p = 0.154).
In terms of the COPAP velocity and COPAP RMS, no significant differences were observed between the Group (COPAP velocity F 2, 31 = 0.443, p = 0.646; COPAP RMS F 2, 31 = 2.199, p = 0.128) and Test session factors (COPAP velocity F 1, 31 = 2.544, p = 0.121; COPAP RMS F 1, 31 = 3.106, p = 0.088). No significant interaction (COPAP velocity F 2, 31 = 1.520, p = 0.235; COPAP RMS F 2, 31 = 0.797, p = 0.460; Table 2) was observed.
With regard to COMML velocity and COMML RMS, no significant main effect was observed for the factor Group (COMML velocity F 2, 31 = 2.329, p = 0.114; COMML RMS F 2, 31 = 2.842, p = 0.074), nor was there a significant interaction (COMML velocity F 2, 31 = 0.121, p = 0.887; COMML RMS F 2, 31 = 2.049, p = 0.146). In contrast, the COMML velocity and COMML RMS showed significant main effects for the factor Test session (COMML velocity F 1, 31 = 12.497, p = 0.001; COMML RMS F 1, 31 = 8.57, p = 0.006). The post hoc test revealed that the post-session COMML velocity of the COP group was significantly lower than that for the pre-session (p = 0.04). However, in the COP + COG and control groups, no significant difference was observed between the sessions (COP + COG group, p = 0.125; control group, p = 0.056). Meanwhile, the post-session COMML RMS of the COP group was significantly higher than that for the pre-session (p = 0.009). The COMML RMS of the COP + COG and control groups showed no significant difference between the sessions (COP + COG group, p = 0.82; control group, p = 0.114).
With regard to COPML velocity, no significant main effect was observed for the factor Group (F 2, 31 = 0.722, p = 0.494), nor was there a significant interaction (F 2, 31 = 0.526, p = 0.596). On the contrary, the COPML velocity presented a significant main effect for the factor Test session (F 1, 31 = 15.86, p < 0.001). The post hoc test revealed that the post-session COPML velocity of the COP group was significantly lower than that for the pre-session (p < 0.001). However, in the COP + COG and control groups, no significant difference was found between the sessions (COP + COG group, p = 0.081; control group, p = 0.195).
Meanwhile, the COPML RMS demonstrated no significant differences between the Group (F 2, 31 = 2.697, p = 0.083) and Test session factors (F 1, 31 = 0.24, p = 0.628). No significant interaction (F 2, 31 = 0.789, p = 0.463) was observed.
In terms of COP − COMclose, no significant effects were observed for the factor Group (F 2, 31 = 1.457, p = 0.248) and no significant interaction (F 2, 31 = 1.267, p = 0.296) was observed. On the other hand, the factor Test session showed significant discrepancies (F 1, 31 = 11.884, p = 0.002; Fig. 3b).
The mean absolute velocity of the COM has been proven to be a highly reliable and sensitive indicator of postural sway [18, 19]. The main finding of this study is that the COMAP velocity decreased after the training session in the COP + COG and control groups, but not in the COP group. The COMAP velocity in the COP + COG group was lower than that in the control group during post-session quiet standing (Table 2). Furthermore, the COMAP RMS was significantly lower in the COP + COG group compared to that in the control group following training. These results suggest that training conducted using simultaneous COPAP and COGAP visual feedback increases postural stability compared to training using the COPAP alone under a no-feedback condition. Therefore, the results of this study have confirmed the hypothesis.
The effects that were related to a decrease in the post-session COMAP velocity would be enhanced by even fluctuations of the COPAP around the COGAP (Fig. 3a) because of the significant correlation between the COMAP velocity and COP − COMeven (Fig. 4a). According to the inverted pendulum model, inertial forces produced by even fluctuations of the COP toward the COG restrain COM movements toward the center of its fluctuation range; this is because the COP − COM distance reflects the moment arm for inertial forces, such as propulsion toward the COM or braking against movements toward the COM [20, 21].
Interestingly, the COPAP velocity did not decrease even though the COMAP velocity decreased in the post-session for each group (Table 2). In general, minimizing the COM displacement would be expected to result in a concurrent decrease in the COP displacement . However, Carpenter et al.  and Murnaghan et al.  showed that COP displacements increased when COM movements were stabilized. They proposed that COP fluctuations played an exploratory role, gathering sensory information during quiet standing. The results of this study indicate that a decrease in the COMAP velocity do not result in a concurrent decrease in the COPAP velocity; as such, the COP and COM velocities may realistically behave in different ways.
No significant differences of the velocity and the RMS of COM and COP between the pre- and post-sessions were found in the COP + COG group in the ML direction. Therefore, the decreased postural stability in the ML direction after the training could not be confirmed in the COP + COG group. Interestingly, the COMML and COPML velocities in the COP group decreased after the training. However, the increased postural stability in the ML direction could not be confirmed because the COMML RMS in the COP group increased after the training. The standing postural controls for the AP or ML direction are involved in two distinct ankle and hip mechanisms . The possibility effects of the postural control during quiet standing between the two mechanisms by the feedback training should be further investigated in future studies .
We suspect that efforts to maintain the COPAP at an even distance from the COGAP may have indirectly contributed to reducing the COP − COM distance; however, no interaction was observed in terms of COP − COMclose. The quantitative results of this study showed that the COMAP velocity was correlated to COP − COMclose (Fig. 4b). Therefore, adding visual targets indicating the COPAP and COGAP (e.g., two other horizontal lines positioned along the centers of the blank circle representing the COPAP and the filled circle representing the COGAP) and requiring participants to reduce the distance between these two horizontal lines may also be effective to decelerate the COMAP velocity.
The limitation of this study is that experiments were performed with a small sample size of participants. In addition, the adaptation effects of training may not be detected sufficiently with the small amount of training the participants underwent. Therefore, the training effects in the COP group may not be detected, although the COMAP velocity in the control group decreased after training. Furthermore, the force under the feet may not be identical to that under the foam pad because the force or moment could spread in the pad. The learning effects of this novel balance training should be further investigated with a retention test and applied to individuals with postural instability in future studies.
Simultaneous visual feedback training that uses both the COPAP and COGAP, and focuses on their interaction, reduces postural sway during quiet standing better than the training designed to affect only the COPAP under the no-feedback condition. It can therefore be stated that even COPAP fluctuations around the COGAP would be effective for maintaining postural static balance through an associated reduction in COMAP velocity.
This work was supported in part by a Japanese Grant-in-Aid for Scientific Research (25350747, 16K16420).
Availability of data and materials
The datasets during and/or analyzed during the current study are available from the corresponding author on reasonable request.
TA, KT, and HMan designed the study. TA and HMae supervised the project. KT, HMan, NH, YS, and ST recorded, analyzed, and interpreted the data. TA and KT wrote the manuscript. All authors read and approved the final manuscript.
Ethics approval and consent to participate
All participants gave written informed consent after a complete explanation of this study. This study was approved by the Institutional Review Board, Faculty of Health Sciences of Hokkaido University.
Consent for publication
All participants gave written informed consent for publication after a complete explanation of this study.
The authors declare that they have no competing interests.
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- Shumway-Cook A, Wollacott M. Motor control: translating research into clinical practice. 4th ed. Philadelphia: Lippincott Williams &Wilkins; 2011.Google Scholar
- Riach CL, Starkes JL. Stability limits of quiet standing postural control in children and adults. Gait Posture. 1993;1:105–11.View ArticleGoogle Scholar
- Winter DA. Biomechanics and motor control of human movement. 4th ed. Hoboken: Wiley; 2009.View ArticleGoogle Scholar
- Dault MC, de Haart M, Geurts ACH, Arts IMP, Nienhuis B. Effects of visual center of pressure feedback on postural control in young and elderly healthy adults and in stroke patients. Hum Mov Sci. 2003;22:221–36.View ArticlePubMedGoogle Scholar
- Zijlstra A, Mancini M, Chiari L, Zijlstra W. Biofeedback for training balance and mobility tasks in older populations: a systematic review. J Neuroeng Rehabil. 2010;7:58.View ArticlePubMedPubMed CentralGoogle Scholar
- Halicka Z, Lovotkova J, Buckova K, Hlavacka F. Effectiveness of different visual biofeedback signals for human balance improvement. Gait Posture. 2014;39:410–4.View ArticlePubMedGoogle Scholar
- Geiger RA, Allen JB, O’Keefe J, Hicks RR. Balance and mobility following stroke: effects of physical therapy interventions with and without biofeedback/forceplate training. Phys Ther. 2001;81:995–1005.PubMedGoogle Scholar
- Freitas SMSF, Duarte M. Joint coordination in young and older adults during quiet stance: effect of visual feedback of the center of pressure. Gait Posture. 2012;35:83–7.View ArticlePubMedGoogle Scholar
- Kilby MC, Slobounov SM, Newell KM. Augmented feedback of COM and COP modulates the regulation of quiet human standing relative to the stability boundary. Gait Posture. 2016;47:18–23.View ArticlePubMedGoogle Scholar
- Lakhani B, Mansfield A. Visual feedback of the centre of gravity to optimize standing balance. Gait Posture. 2015;41:499–503.View ArticlePubMedGoogle Scholar
- Corriveau H, Hebert R, Prince F, Raiche M. Postural control in the elderly: an analysis of test-retest and interrater reliability of the COP-COM variable. Arch Phys Med Rehab. 2001;82:80–5.View ArticleGoogle Scholar
- Masani K, Vette AH, Kouzaki M, Kanehisa H, Tukunaga T, Popovic MR. Larger center of pressure minus center of gravity in the elderly induces larger body acceleration during quiet standing. Neurosci Lett. 2007;422:202–6.View ArticlePubMedGoogle Scholar
- Yu E, Abe M, Masani K, Kawashima N, Eto F, Haga N, Nakazawa K. Evaluation of postural control in quiet standing using center of mass acceleration: comparison among the young, the elderly, and people with stroke. Arch Phs Med Rehabil. 2008;89:1133–9.View ArticleGoogle Scholar
- Mani H, Hsiao SF, Takeda K, Hasegawa N, Tozuka M, Tsuda A, Ohashi T, Suwahara T, Ito K, Asaka T. Age-related changes in distance from center of mass to center of pressure during one-leg standing. J Mot Behav. 2015;47:282–90.View ArticlePubMedGoogle Scholar
- Ibuki A, Mani H, Takeda K, Hasegawa N, Yamamoto K, Maejima H, Asaka T: Characteristic relationship between the centre of pressure and the centre of mass during quiet standing in female ballet dancers. Int Phys Med Rehab J 2017; DOI: 10.15406/ipmrj.2017.01.00009
- Cawsey RP, Cha R, Carpenter MG, Sanderson DJ. To what extent can increasing the magnification of visual feedback of the centre of pressure position change the control of quiet standing balance? Gait Posture. 2009;29:280–4.View ArticlePubMedGoogle Scholar
- Okuni I, Uchi M, Harada T. Sagittal-plane spinal curvature and center of foot pressure in healthy young adults. J Med Soc Toho Univ. 2006;53:254–60.Google Scholar
- Raymakers JA, Samson MM, Verhaar HJ. The assessment of body sway and the choice of the stability parameter(s). Gait Posture. 2005;21:48–58.View ArticlePubMedGoogle Scholar
- van Dieen JH, Koppes LL, Twisk JW. Postural sway parameters in seated balancing; their reliability and relationship with balancing performance. Gait Posture. 2010;31:42–6.View ArticlePubMedGoogle Scholar
- Chang H, Krebs DE. Dynamic balance control in elders: gait initiation assessment as a screening tool. Arch Phs Med Rehabil. 1999;80:490–4.View ArticleGoogle Scholar
- Jian Y, Winter DA, Ishac MG, Gilchrist L. Trajectory of the body COG and COP during initiation and termination of gait. Gait Posture. 1993;1:9–22.View ArticleGoogle Scholar
- Horak FB, MacPherson JM. Postural orientation and equilibrium. In: Rowell LB, Shepherd JT, editors. Handbook of physiology, section 12, exercise: regulation and Integration of Multiple Systems. New York: Oxford University Press; 1996. p. 255–92.Google Scholar
- Carpenter MG, Murnaghan CD, Inglis JT. Shifting the balance: evidence of an exploratory role for postural sway. Neuroscience. 2010;171:196–204.View ArticlePubMedGoogle Scholar
- Murnaghan CD, Horslen BC, Inglis JT, Carpenter MG. Exploratory behaviour during stance persists with visual feedback. Neuroscience. 2011;195:54–9.View ArticlePubMedGoogle Scholar
- Rougier PR. Undisturbed stance control in healthy adults is achieved differently along anteroposterior and mediolateral axes: evidence from visual feedback of various signals from center of pressure trajectories. J Mot Behav. 2009;41:197–206.View ArticlePubMedGoogle Scholar