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<?xml version="1.0" encoding="UTF-8" ?><xml><records><record><database name="stability.enl" path="/Users/sjoerd/Dropbox/Endnote library/stability.enl">stability.enl</database><source-app name="EndNote" version="18.2">EndNote</source-app><rec-number>3330</rec-number><foreign-keys><key app="EN" db-id="05zd2dwf65r5xeetapvvprt3twdpzww9we55">3330</key></foreign-keys><ref-type name="Journal Article">17</ref-type><contributors><authors><author><style face="normal" font="default" size="100%">Alizadehsaravi, L.</style></author><author><style face="normal" font="default" size="100%">Bruijn, S. M.</style></author><author><style face="normal" font="default" size="100%">Maas, H.</style></author><author><style face="normal" font="default" size="100%">van Dieen, J. H.</style></author></authors></contributors><auth-address><style face="normal" font="default" size="100%">Department of Human Movement Sciences, Faculty of Behavioural and Movement Sciences, Institute for Brain and Behaviour Amsterdam and Amsterdam Movement Sciences, Vrije Universiteit Amsterdam, Van der Boechorststraat 9, 1081 BT, Amsterdam, The Netherlands.
Department of Human Movement Sciences, Faculty of Behavioural and Movement Sciences, Institute for Brain and Behaviour Amsterdam and Amsterdam Movement Sciences, Vrije Universiteit Amsterdam, Van der Boechorststraat 9, 1081 BT, Amsterdam, The Netherlands. [email protected].</style></auth-address><titles><title><style face="normal" font="default" size="100%">Modulation of soleus muscle H-reflexes and ankle muscle co-contraction with surface compliance during unipedal balancing in young and older adults</style></title><secondary-title><style face="normal" font="default" size="100%">Exp Brain Res</style></secondary-title></titles><periodical><full-title><style face="normal" font="default" size="100%">Exp Brain Res</style></full-title><abbr-1><style face="normal" font="default" size="100%">Experimental brain research. Experimentelle Hirnforschung. Experimentation cerebrale</style></abbr-1></periodical><pages><style face="normal" font="default" size="100%">1371-1383</style></pages><volume><style face="normal" font="default" size="100%">238</style></volume><number><style face="normal" font="default" size="100%">6</style></number><edition><style face="normal" font="default" size="100%">2020/04/09</style></edition><keywords><keyword><style face="normal" font="default" size="100%">Aging</style></keyword><keyword><style face="normal" font="default" size="100%">Balance control</style></keyword><keyword><style face="normal" font="default" size="100%">Co-contraction</style></keyword><keyword><style face="normal" font="default" size="100%">H-reflex</style></keyword><keyword><style face="normal" font="default" size="100%">Postural control</style></keyword><keyword><style face="normal" font="default" size="100%">Spinal excitability</style></keyword></keywords><dates><year><style face="normal" font="default" size="100%">2020</style></year><pub-dates><date><style face="normal" font="default" size="100%">Jun</style></date></pub-dates></dates><isbn><style face="normal" font="default" size="100%">1432-1106 (Electronic)
0014-4819 (Linking)</style></isbn><accession-num><style face="normal" font="default" size="100%">32266445</style></accession-num><abstract><style face="normal" font="default" size="100%">This study aimed to assess modulation of lower leg muscle reflex excitability and co-contraction during unipedal balancing on compliant surfaces in young and older adults. Twenty healthy adults (ten aged 18-30 years and ten aged 65-80 years) were recruited. Soleus muscle H-reflexes were elicited by electrical stimulation of the tibial nerve, while participants stood unipedally on a robot-controlled balance platform, simulating different levels of surface compliance. In addition, electromyographic data (EMG) of soleus (SOL), tibialis anterior (TA), and peroneus longus (PL) and full-body 3D kinematic data were collected. The mean absolute center of mass velocity was determined as a measure of balance performance. Soleus H-reflex data were analyzed in terms of the amplitude related to the M wave and the background EMG activity 100 ms prior to the stimulation. The relative duration of co-contraction was calculated for soleus and tibialis anterior, as well as for peroneus longus and tibialis anterior. Center of mass velocity was significantly higher in older adults compared to young adults ([Formula: see text] and increased with increasing surface compliance in both groups ([Formula: see text]. The soleus H-reflex gain decreased with surface compliance in young adults [Formula: see text], while co-contraction increased [Formula: see text]. Older adults did not show such modulations, but showed overall lower H-reflex gains [Formula: see text] and higher co-contraction than young adults [Formula: see text]. These results suggest an overall shift in balance control from the spinal level to supraspinal levels in older adults, which also occurred in young adults when balancing at more compliant surfaces.</style></abstract><notes><style face="normal" font="default" size="100%">Alizadehsaravi, Leila
Bruijn, Sjoerd M
Maas, Huub
van Dieen, Jaap H
eng
Germany
Exp Brain Res. 2020 Jun;238(6):1371-1383. doi: 10.1007/s00221-020-05784-0. Epub 2020 Apr 7.</style></notes><urls><related-urls><url><style face="normal" font="default" size="100%">https://www.ncbi.nlm.nih.gov/pubmed/32266445</style></url><url><style face="normal" font="default" size="100%">https://www.ncbi.nlm.nih.gov/pmc/articles/PMC7286858/pdf/221_2020_Article_5784.pdf</style></url></related-urls><pdf-urls><url>internal-pdf://3172685974/Alizadehsaravi-2020-Modulation of soleus muscl.pdf</url></pdf-urls></urls><custom2><style face="normal" font="default" size="100%">PMC7286858</style></custom2><electronic-resource-num><style face="normal" font="default" size="100%">10.1007/s00221-020-05784-0</style></electronic-resource-num></record><record><database name="stability.enl" path="/Users/sjoerd/Dropbox/Endnote library/stability.enl">stability.enl</database><source-app name="EndNote" version="18.2">EndNote</source-app><rec-number>3332</rec-number><foreign-keys><key app="EN" db-id="05zd2dwf65r5xeetapvvprt3twdpzww9we55">3332</key></foreign-keys><ref-type name="Journal Article">17</ref-type><contributors><authors><author><style face="normal" font="default" size="100%">van den Bogaart, M.</style></author><author><style face="normal" font="default" size="100%">Bruijn, S. M.</style></author><author><style face="normal" font="default" size="100%">van Dieen, J. H.</style></author><author><style face="normal" font="default" size="100%">Meyns, P.</style></author></authors></contributors><auth-address><style face="normal" font="default" size="100%">Rehabilitation Research Center (REVAL), Faculty of Rehabilitation Sciences, Hasselt University, Diepenbeek 3590, Belgium; MOVE Research Institute Amsterdam, Department of Human Movement Sciences, Faculty of Behavioural and Movement Sciences, Vrije Universiteit Amsterdam, Amsterdam 1081 BT, the Netherlands.
MOVE Research Institute Amsterdam, Department of Human Movement Sciences, Faculty of Behavioural and Movement Sciences, Vrije Universiteit Amsterdam, Amsterdam 1081 BT, the Netherlands; Institute Brain and Behaviour Amsterdam, Amsterdam, The Netherlands. Electronic address: [email protected].
MOVE Research Institute Amsterdam, Department of Human Movement Sciences, Faculty of Behavioural and Movement Sciences, Vrije Universiteit Amsterdam, Amsterdam 1081 BT, the Netherlands.
Rehabilitation Research Center (REVAL), Faculty of Rehabilitation Sciences, Hasselt University, Diepenbeek 3590, Belgium.</style></auth-address><titles><title><style face="normal" font="default" size="100%">The effect of anteroposterior perturbations on the control of the center of mass during treadmill walking</style></title><secondary-title><style face="normal" font="default" size="100%">J Biomech</style></secondary-title></titles><periodical><full-title><style face="normal" font="default" size="100%">J Biomech</style></full-title><abbr-1><style face="normal" font="default" size="100%">Journal of biomechanics</style></abbr-1></periodical><pages><style face="normal" font="default" size="100%">109660</style></pages><volume><style face="normal" font="default" size="100%">103</style></volume><edition><style face="normal" font="default" size="100%">2020/03/17</style></edition><keywords><keyword><style face="normal" font="default" size="100%">Ankle moments</style></keyword><keyword><style face="normal" font="default" size="100%">Center of mass acceleration</style></keyword><keyword><style face="normal" font="default" size="100%">Counter-rotation mechanism</style></keyword><keyword><style face="normal" font="default" size="100%">Foot placement</style></keyword><keyword><style face="normal" font="default" size="100%">Gait stability</style></keyword><keyword><style face="normal" font="default" size="100%">Perturbed treadmill walking</style></keyword><keyword><style face="normal" font="default" size="100%">competing financial interests or personal relationships that could have appeared</style></keyword><keyword><style face="normal" font="default" size="100%">to influence the work reported in this paper.</style></keyword></keywords><dates><year><style face="normal" font="default" size="100%">2020</style></year><pub-dates><date><style face="normal" font="default" size="100%">Apr 16</style></date></pub-dates></dates><isbn><style face="normal" font="default" size="100%">1873-2380 (Electronic)
0021-9290 (Linking)</style></isbn><accession-num><style face="normal" font="default" size="100%">32171496</style></accession-num><abstract><style face="normal" font="default" size="100%">Shifts of the center of pressure (CoP) through modulation of foot placement and ankle moments (CoP-mechanism) cause accelerations of the center of mass (CoM) that can be used to stabilize gait. An additional mechanism that can be used to stabilize gait, is the counter-rotation mechanism, i.e., changing the angular momentum of segments around the CoM to change the direction of the ground reaction force. The relative contribution of these mechanisms to the control of the CoM is unknown. Therefore, we aimed to determine the relative contribution of these mechanisms to control the CoM in the anteroposterior (AP) direction during a normal step and the first recovery step after perturbation in healthy adults. Nineteen healthy subjects walked on a split-belt treadmill and received unexpected belt acceleration perturbations of various magnitudes applied immediately after right heel-strike. Full-body kinematic and force plate data were obtained to calculate the contributions of the CoP-mechanism and the counter-rotation mechanism to control the CoM. We found that the CoP-mechanism contributed to corrections of the CoM acceleration after the AP perturbations, while the counter-rotation mechanism actually counteracted the CoM acceleration after perturbation, but only in the initial phases of the first step after the perturbation. The counter-rotation mechanism appeared to prevent interference with the gait pattern, rather than using it to control the CoM after the perturbation. Understanding the mechanisms used to stabilize gait may have implications for the design of therapeutic interventions that aim to decrease fall incidence.</style></abstract><notes><style face="normal" font="default" size="100%">van den Bogaart, Maud
Bruijn, Sjoerd M
van Dieen, Jaap H
Meyns, Pieter
eng
J Biomech. 2020 Apr 16;103:109660. doi: 10.1016/j.jbiomech.2020.109660. Epub 2020 Jan 24.</style></notes><urls><related-urls><url><style face="normal" font="default" size="100%">https://www.ncbi.nlm.nih.gov/pubmed/32171496</style></url><url><style face="normal" font="default" size="100%">https://pdf.sciencedirectassets.com/271132/1-s2.0-S0021929020X00066/1-s2.0-S0021929020300671/main.pdf?X-Amz-Security-Token=IQoJb3JpZ2luX2VjEHYaCXVzLWVhc3QtMSJHMEUCIDvGAuRndPJe%2FWROLn53Dga5nrdNB7JMSVFywzx56TibAiEA6%2BWz3Lp3xZUoxTK3b0gGebn7XO4yzm0rH8wJbgzKbUcqtAMILxADGgwwNTkwMDM1NDY4NjUiDFuSRJDtGElzr61iryqRA0aIccelxHXm0MwdMAiHRSzJj2ldr8qpgQiQsNE1JvgYbWx4xKOOwTyA%2FBCdsYTyp48pfNcuy%2BhrkcikCw8zGewB3GhOPF6TXGaTs4E7MqI4GX3V%2BZHJDlsXSq318ht0zHJDSUKGptWU3WvW6cBFwhI35qX6v12JokDpPtYtw5jv7dv0SbP0Q%2F1ra%2Bx0yyKNgVWPb8izjcP2Uie2LQNa8LZbuLY4t%2FlhzH%2BDtpI5HNT8NsA4BWdaiDV9v%2FWpA8TfUb07JIBYRc7W0v3%2B%2F9ju%2FXvk1CR5hnWUTYeRUtrYhb6TQJcMTsKAV7tm6kXIG8U%2BdRF0NN5HexhVR5m9CKBK9hEEghmtt7MrY3At9OrAeHkDeez2TOo9sdgKBp4W8GndmXhRs3jaIZ5AIAYHMd%2Bq0RF2hzkSH%2FycytsHjR542sj2jCdgp8NJTrvVePjPVwgvjgV4kfsTDYUU3nvvM34wkpx7s2s5m2uJmBWhbX%2BCRU4QYLim5iHuEAftA8KEWmXiYgzMYfuEMUII9OJxnCQNbyJVMM651vgFOusBTDtZdGXWMMv5%2BpcDh8OwgSwuRhcCiQpXyhei88hOF2nVygtA0CYI5Wj0%2BCsxLyodGxPA7L%2FWEpii52KYQB3bcL%2FmDxUojRXo3HpjLYxGtdFcDtnYcXc7PHOmC00VDgdO6F1rVd50Uq%2BvJxZB8JheFoqO%2Bai8keeZgF1fzi22FOMAj4h4Mh1sR9LSn72kPd2%2BFTrjQDCzBBydrTnMYKe7iLaQo8%2Fzs1OxFtbXSRDCJgxVXnx9QcgxGBmalzXJDLhJP6VmX1YxoyIn6LN%2FCoUU94uBjJty%2FyyLM35va2nGsPcA7sASvHQFYWzOKQ%3D%3D&X-Amz-Algorithm=AWS4-HMAC-SHA256&X-Amz-Date=20200720T142911Z&X-Amz-SignedHeaders=host&X-Amz-Expires=300&X-Amz-Credential=ASIAQ3PHCVTY2FJYE7EH%2F20200720%2Fus-east-1%2Fs3%2Faws4_request&X-Amz-Signature=d15e6dc73187740aef7f39bcee645cd2267019cabcf83904c9951d499de36c30&hash=105eca4989bec123fed651c35d5d3461f2c548bd55ea2eccb4a79e932f8ea6c6&host=68042c943591013ac2b2430a89b270f6af2c76d8dfd086a07176afe7c76c2c61&pii=S0021929020300671&tid=spdf-0320fe38-9554-4369-a0c4-e9cc0ac132f5&sid=67b6f89490d3f94ce86b9242a40ecea97a17gxrqb&type=client</style></url></related-urls><pdf-urls><url>internal-pdf://3829176373/van den Bogaart-2020-The effect of anteroposte.pdf</url></pdf-urls></urls><electronic-resource-num><style face="normal" font="default" size="100%">10.1016/j.jbiomech.2020.109660</style></electronic-resource-num></record></records></xml>