Financement des sociétés américaines et internationales de biomécanique a été fournie pour cette étude.

<ol>
	<li>Chandler, R. F., Clauser, C. E., McConville, J. T., Reynolds, H. M., Young, S. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Investigation+of+the+inertial+properties+of+the+human+body.">Investigation of the inertial properties of the human body.</a> Pamphlets DOT HS-801 430 and AMRL. , (1975).</li><li>Clauser, C. E., McConville, J. T., Young, J. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=.">.</a> Weight, Volume, and Center of Mass of Segments of the Human Body. AMRL Technical Report. , 60-70 (1969).</li><li>Dempster, W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Space+requirements+of+the+seated+operator.">Space requirements of the seated operator.</a> , 55-159 (1955).</li><li>Hinrichs, R. N., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Regression+equations+to+predict+segmental+moments+of+inertia+from+anthropometric+measurements:+an+extension+of+the+data+of+Chandler+et.">Regression equations to predict segmental moments of inertia from anthropometric measurements: an extension of the data of Chandler et.</a> J Biomech. 18, 621-624 (1985).</li><li>Hinrichs, R. N., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Adjustments+to+the+segment+center+of+mass+proportions+of+Clauser+et+al.">Adjustments to the segment center of mass proportions of Clauser et al.</a> J Biomech. 23, 949-951 (1990).</li><li>Hanavan Jr, E. 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E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Estimating+segment+inertial+properties:+comparison+of+magnetic+resonance+imaging+with+existing+methods.">Estimating segment inertial properties: comparison of magnetic resonance imaging with existing methods.</a> J Biomech. 23, 1039-1046 (1990).</li><li>Zatsiorsky, V. M., Seluyanov, V. N. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+mass+and+inertia+characteristics+of+the+main+segments+of+the+human+body.">The mass and inertia characteristics of the main segments of the human body.</a> Biomechanics VIII-B. , 1152-1159 (1983).</li><li>Zatsiorsky, V. M., Seluyanov, V. N. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Biomechanics+IX-B.">Biomechanics IX-B.</a> Human Kinetics. , (1985).</li><li>Challis, J. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Precision+of+the+Estimation+of+Human+Limb+Inertial+Parameters.">Precision of the Estimation of Human Limb Inertial Parameters.</a> Journal of Applied Biomechanics. 15, 418-428 (1999).</li><li>Challis, J. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Accuracy+of+Human+Limb+Moment+of+Inertia+Estimations+and+Their+Influence+on+Resultant+Joint+Moments.">Accuracy of Human Limb Moment of Inertia Estimations and Their Influence on Resultant Joint Moments.</a> Journal of Applied Biomechanics. 12, 517-530 (1996).</li><li>Challis, J. H., Kerwin, D. G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Quantification+of+the+uncertainties+in+resultant+joint+moments+computed+in+a+dynamic+activity.">Quantification of the uncertainties in resultant joint moments computed in a dynamic activity.</a> J Sports Sci. 14, 219-231 (1996).</li><li>Hunter, J. P., Marshall, R. N., McNair, P. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Segment-interaction+analysis+of+the+stance+limb+in+sprint+running.">Segment-interaction analysis of the stance limb in sprint running.</a> J Biomech. 37, 1439-1446 (2004).</li><li>Lin-Chan, S. J., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+effects+of+added+prosthetic+mass+on+physiologic+responses+and+stride+frequency+during+multiple+speeds+of+walking+in+persons+with+transtibial+amputation.">The effects of added prosthetic mass on physiologic responses and stride frequency during multiple speeds of walking in persons with transtibial amputation.</a> Arch Phys Med Rehabil. 84, 1865-1871 (2003).</li><li>Mattes, S. J., Martin, P. E., Royer, T. D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Walking+symmetry+and+energy+cost+in+persons+with+unilateral+transtibial+amputations:+matching+prosthetic+and+intact+limb+inertial+properties.">Walking symmetry and energy cost in persons with unilateral transtibial amputations: matching prosthetic and intact limb inertial properties.</a> Arch Phys Med Rehabil. 81, 561-568 (2000).</li><li>Smith, J. D., Martin, P. E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Short+and+longer+term+changes+in+amputee+walking+patterns+due+to+increased+prosthesis+inertia.">Short and longer term changes in amputee walking patterns due to increased prosthesis inertia.</a> J Prosthet Orthot. 23, 114-123 (2011).</li><li>Smith, J. D., Martin, P. E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Effects+of+prosthetic+mass+distribution+on+metabolic+costs+and+walking+symmetry.">Effects of prosthetic mass distribution on metabolic costs and walking symmetry.</a> J Appl Biomech. 29, 317-328 (2013).</li><li>Czerniecki, J. M., Gitter, A., Munro, C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Joint+moment+and+muscle+power+output+characteristics+of+below+knee+amputees+during+running:+the+influence+of+energy+storing+prosthetic+feet.">Joint moment and muscle power output characteristics of below knee amputees during running: the influence of energy storing prosthetic feet.</a> J Biomech. 24, 63-75 (1991).</li><li>Miller, D. I. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Resultant+lower+extremity+joint+moments+in+below-knee+amputees+during+running+stance.">Resultant lower extremity joint moments in below-knee amputees during running stance.</a> J Biomech. 20, 529-541 (1987).</li><li>Vanicek, N., Strike, S., McNaughton, L., Polman, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Gait+patterns+in+transtibial+amputee+fallers+vs.+non-fallers:+Biomechanical+differences+during+level+walking.">Gait patterns in transtibial amputee fallers vs. non-fallers: Biomechanical differences during level walking.</a> Gait &amp; Posture. 29, 415-420 (2009).</li><li>Royer, T., Koenig, M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Joint+loading+and+bone+mineral+density+in+persons+with+unilateral,+trans-tibial+amputation.">Joint loading and bone mineral density in persons with unilateral, trans-tibial amputation.</a> Clin Biomech. 20, 1119-1125 (2005).</li><li>Underwood, H. A., Tokuno, C. D., Eng, J. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+comparison+of+two+prosthetic+feet+on+the+multi-joint+and+multi-plane+kinetic+gait+compensations+in+individuals+with+a+unilateral+trans-tibial+amputation.">A comparison of two prosthetic feet on the multi-joint and multi-plane kinetic gait compensations in individuals with a unilateral trans-tibial amputation.</a> Clin Biomech. 19, 609-616 (2004).</li><li>Sjodahl, C., Jarnlo, G. B., Soderberg, B., Persson, B. 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Les auteurs déclarent qu&#39;ils n&#39;ont aucun intérêt financier concurrents.

Pour quantifier les forces et moments communs obtenus pendant le mouvement, un modèle du système d&#39;intérêt de dynamique inverse est nécessaire lorsque l&#39;on travaille avec des données empiriques. Pour la biomécanique des membres inférieurs, des modèles de dynamique inverse représentent généralement le pied, le jambonneau, et la cuisse corps rigides. Entrée pour ces modèles proviennent de trois sources principales: a) mouvement cinématique, b) des forces de réaction au sol, et c) anthropométriques de segment et propriétés d&#39;inertie. les données de mouvement sont collectées avec une variété de systèmes d&#39;analyse de mouvement, mais tous les systèmes fournissent essentiellement la cinématique de base du mouvement (position, vitesse et accélération). les forces de réaction au sol sont recueillies avec un plateau de force et de fournir les forces de contact agissant sur les pieds. Anthropométriques sont des mesures prises directement à partir du corps à l&#39;aide de règles, de bandes flexibles, et / ou étriers. Ces mesures anthropométriques sont utilisées pour estimer les propriétés d&#39;inertie des segments corporels utilisés dans la dynamiquement inversecs analyse. Propriétés d&#39;inertie comprennent la masse, centre de masse (COM) l&#39;emplacement et le moment d&#39;inertie (MOI) du segment par rapport à un axe passant par le COM de segment ou proximale ou distale commune. Méthodes et l&#39;équipement utilisés pour la collecte de données et le mouvement des forces de réaction au sol sont similaires entre les groupes de recherche, mais les estimations d&#39;inertie des segments corporels peuvent varier considérablement entre les chercheurs en fonction de la méthode que le chercheur choisit pour estimer ces propriétés d&#39;inertie. Diverses techniques disponibles pour l&#39;estimation des propriétés d&#39;inertie d&#39;un segment intact du corps humain comprennent: 1) des équations de régression basés sur les données de cadavres 1-5, 2) techniques des modèles mathématiques (c.-à-modèles géométriques) 6,7, et 3) numérisation et d&#39;imagerie 8-15. Beaucoup de ces techniques nécessitent des mesures directes de l&#39;organisme, mais il a été montré précédemment que, indépendamment de la méthode d&#39;estimation utilisée, la précision des segments du corpsestimations d&#39;inertie ment sur ​​la base de ces méthodes est élevé 16. Il a également été montré que les erreurs dans les estimations des propriétés d&#39;inertie des segments du corps intacts ont un impact minimal sur l&#39;ampleur des moments communs obtenus lors de la marche 17,18. Joint moments sont influencées dans une grande mesure par des forces de réaction au sol, les emplacements de centre de pression, des longueurs de bras de moment, et de la cinématique de segment de 17 à 19. Par conséquent, il n&#39;est pas surprenant que les méthodes d&#39;estimation des propriétés d&#39;inertie des segments corporels varient considérablement la littérature lors de l&#39;utilisation des personnes valides comme participants à la recherche, étant donné que de petites erreurs dans ces estimations sont susceptibles d&#39;avoir peu d&#39;impact sur les résultats de l&#39;étude. Beaucoup de ces estimations d&#39;inertie pour un segment de corps intact sont souvent utilisés pour estimer les propriétés d&#39;inertie de prothèses pour les amputés des membres inférieurs. Modernes prothèses des membres inférieurs sont fabriqués avec des matériaux légers résultating dans les prothèses qui sont beaucoup plus légers que les membres qu&#39;ils remplacent. Il en résulte une dissymétrie d&#39;inertie entre la prothèse et l&#39;intégrité physique intacte. Par rapport à une tige typique intact et du pied, la masse d&#39;une prothèse tibiale et membre résiduel est d&#39;environ 35% de moins et a un centre de gravité situé à environ 35% plus près de l&#39;articulation du genou de 20 à 23. La masse plus faible et de la distribution de masse plus proximale de la prothèse produit également un (~ 60%) Le moment d&#39;inertie beaucoup plus faible par rapport à l&#39;articulation du genou pour la prothèse par rapport à celui de la tige et le pied intact. Bien que les chercheurs 24,25 ont déjà suggéré que l&#39;utilisation des estimations d&#39;inertie intactes pour la prothèse ont peu d&#39;effet sur ​​les estimations cinétiques communes, ces comparaisons ont porté sur les moments communs obtenus lors de la phase d&#39;appui de la marche, où la force de réaction du sol domine le moment produit à l&#39; conjointe. Au cours de swing, où les forces de réaction au sol ne sont pas présents, lapropriétés d&#39;inertie réduite de la prothèse sont plus susceptibles d&#39;influer sur les estimations de moments communs qui en découlent. Étant donné que certains chercheurs, par exemple, 26-32 utilisent intactes les propriétés d&#39;inertie du segment pour représenter prothèse propriétés d&#39;inertie et d&#39;autres, par exemple 21-23 estimation prothèse propriétés d&#39;inertie directement, il est important de comprendre l&#39;impact des méthodes choisies pour estimer les propriétés d&#39;inertie de la prothèse . En réduisant le temps nécessaire pour mesurer les propriétés d&#39;inertie de la prothèse était une considération importante dans le développement de notre technique. Dans la technique présentée ici la prothèse reste intact pour toutes les mesures pour réduire les temps de mesure et à éviter les temps additionnels associés à réaligner la prothèse après la mesure. Ainsi, le but de cette étude était double: 1) démontrer une technique qui peut être utilisée directement pour estimer les propriétés d&#39;inertie de abProthèse elow genou, et 2) comparer les effets de la technique proposée et que l&#39;utilisation de membre intact les propriétés d&#39;inertie sur des estimations cinétiques communes lors de la marche dans unilatérales, amputés transtibiaux. Il a émis l&#39;hypothèse que les grandeurs cinétiques conjointes sont plus grandes lorsque les propriétés d&#39;inertie de la tige intacte et le pied sont utilisés comme les estimations d&#39;inertie pour la prothèse par rapport à des mesures directes des propriétés d&#39;inertie de la prothèse.

<table border="0" cellpadding="0" cellspacing="0">
	<tbody>
		<tr height="105">
			<td height="105" style="height:105px;width:216px;">Oscillation Rack &#38; Reaction Board</td>
			<td style="width:144px;">Custom Built</td>
			<td style="width:119px;"></td>
			<td style="width:167px;">Outer cage made from 80/20 aluminum, inner cage from various thicknesses of solid of aluminum.</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:216px;">Laboratory scale</td>
			<td style="width:144px;"></td>
			<td style="width:119px;"></td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="63">
			<td height="63" style="height:63px;width:216px;">NI LabView</td>
			<td style="width:144px;">National Instruments</td>
			<td style="width:119px;"></td>
			<td style="width:167px;">Software for recording TTL pulses from infrared photocell.</td>
		</tr>
		<tr height="84">
			<td height="84" style="height:84px;width:216px;">BNC-1050</td>
			<td style="width:144px;">National Instruments</td>
			<td style="width:119px;"></td>
			<td style="width:167px;">BNC Breakout box with direct pin connections to the data acquisition card</td>
		</tr>
		<tr height="105">
			<td height="105" style="height:105px;width:216px;">MATLAB</td>
			<td style="width:144px;">Mathworks Inc.</td>
			<td style="width:119px;"></td>
			<td style="width:167px;">Software for processing oscillation and reaction board data to predict inertial properties of prosthesis.</td>
		</tr>
	</tbody>
</table>

oscillation and reaction board techniques for estimating inertial properties of a below-knee prosthesis

Le but de cette étude était double: 1) démontrer une technique qui peut être utilisée pour estimer directement les propriétés d&#39;inertie d&#39;une prothèse de jambe, et 2) comparer les effets de la technique proposée et que l&#39;utilisation de membre intact les propriétés d&#39;inertie sur des estimations cinétiques communes lors de la marche dans unilatérales, amputés transtibiaux. Un système d&#39;oscillation et le conseil de réaction a été validé et avéré fiable pour mesurer les propriétés d&#39;inertie des solides géométriques connues. Lorsque des mesures directes des propriétés d&#39;inertie de la prothèse ont été utilisés dans la modélisation dynamique inverse de l&#39;extrémité inférieure par rapport aux estimations d&#39;inertie fondés sur une tige intacte et le pied, la cinétique communes de la hanche et du genou étaient significativement plus faibles au cours de la phase d&#39;oscillation de la marche. Les différences dans la cinétique conjointes pendant attitude, cependant, étaient plus petits que ceux observés au cours swing. Par conséquent, les chercheurs se concentrant sur la phase d&#39;oscillation de la marche doivent considérer l&#39;impact de prosthesconstituent des estimations de propriété inertie sur les résultats de l&#39;étude. Pour la position, soit l&#39;un des deux modèles d&#39;inertie étudiés dans notre étude aurait probablement conduire à des résultats similaires avec une évaluation de la dynamique inverse.

Propriétés d&#39;inertie de la branche distale de la prothèse de genou ont été plus faibles que celles de la patte intacte (Tableau 1). En moyenne pour les participants, la masse latérale prothétique était de 39% inférieur, moment d&#39;inertie autour d&#39;un axe transversal par l&#39;intermédiaire du genou était de 52% inférieure, et le centre de localisation de masse a été de 24% plus près du genou comparativement à des valeurs pour la patte intacte. <table border="1" cellpadding="0" cellspacing="0" fo:keep-together.within-page="always" width="553"><tbody><tr><td> Sujet </td><td> Intact * Masse (kg) </td><td> Pour † Masse (kg) </td><td> Est. différence de masse (kg) </td><td> ‡ Iknee intact (kg · m 2) </td><td> pros Iknee (kg · m 2) </td><td> CM intacts au-dessous de l&#39;articulation du genou (m) </td><td> Pros CM-dessous de l&#39;articulation du genou (m) </td></tr><tr><td> A </td><td> 6.03 </td><td> 4.27 </td><td> 1,76 </td><td> 0.604 </td><td> 0,325 </td><td> 0,268 </td><td> 0,215 </td></tr><tr><td> B </td><td> 6.07 </td><td> 3.39 </td><td> 2.68 </td><td> 0.400 </td><td> 0,196 </td><td> 0,215 </td><td> 0,177 </td></tr><tr><td> C </td><td> 5,80 </td><td> 3.12 </td><td> 2.68 </td><td> 0,575 </td><td> 0,194 </td><td> 0,264 </td><td> 0,198 </td></tr><tr><td> Ré </td><td> 5,72 </td><td> 3.17 </td><td> 2.55 </td><td> 0,559 </td><td> 0,317 </td><td> 0,265 </td><td> 0,191 </td></tr><tr><td> E </td><td> 7.14 </td><td> 4,65 </td><td> 2.49 </td><td> 0,742 </td><td> 0,325 </td><td> 0,276 </td><td> 0,200 </td></tr><tr><td> Fa </td><td> 6.23 </td><td> 4.22 </td><td> 2.01 </td><td> 0,585 </td><td> 0,287 </td><td> 0.260 </td><td> 0,192 </td></tr><tr><td> Moyenne ± STD </td><td> 6,17 ± 0,51 </td><td> 3,80 ± 0,66 </td><td> 2,36 ± 0,38 </td><td> 0,578 ± 0,109 </td><td> 0,274 ± 0,063 </td><td> 0,258 et# 177; 0,022 </td><td> 0,196 ± 0,013 </td></tr></tbody></table> * Intact se réfère aux valeurs de la tige intacte combiné et du pied. † Pour se réfère aux valeurs de la prothèse combinée et moignon. ‡ Le moment d&#39;inertie autour d&#39;un axe transversal par l&#39;intermédiaire du genou. Tableau 1. Comparaison des propriétés d&#39;inertie entre les prothèses et intactes du genou. Forces conjointes en résultent (figure 3) et des moments (figure 4) à la cheville, du genou, de la hanche et ont été affectés par les paramètres inertiels utilisés dans le modèle de dynamique inverse. Plus précisément, la cinétique conjointes ont été réduites au cours de balançoire initiation (~ 65% du cycle de marche) et la fin de swing (~ 95% du cycle de marche) lorsque des mesures directes de l&#39;inertie de la prothèse ont été utilisés dans les évaluations de la dynamique inverse par rapport aux régressions fondées sur l&#39;anatomie intacte ( <strong&gt; Tableau 2). L&#39;ampleur des effets suggèrent que ces différences au cours de balançoire ne sont pas trivial (≥ 1,0). En outre, les valeurs cinétiques communes augmenté en moyenne de 80% lors de l&#39;initiation de swing et de résiliation lorsque les estimations d&#39;inertie intactes ont été utilisés par rapport aux mesures directes des propriétés d&#39;inertie de la prothèse. Ainsi, lorsque les propriétés d&#39;inertie d&#39;un membre intact ont été utilisés pour modéliser le côté prothétique, profils cinétiques conjoints du côté prothétique pendant swing plus étroitement ressemblaient à ceux d&#39;un membre intact (voir figures 3 et 4). Au cours de la position, un certain nombre de différences statistiques ont été observées. La plus grande taille de l&#39;effet de toute différence pendant attitude a été observée pour la hanche antéropostérieur force conjointe résultante (ES = 0,86). Bien que la taille de cet effet est important et toujours considérée comme faisant partie de la position, la valeur de crête de cette mesure s&#39;est produite lors de la phase terminale (~ 52%), ou que le membre a été la transition en swing. Les tailles d&#39;effet pour tous les autres significant différences observées au cours de la position variait de 0,01 à 0,41, ce qui serait considéré comme de petits effets avec la plus grande de ces valeurs étant observées dans les forces de réaction de la hanche qui en résultent. Bien que des différences significatives ont été observées lors de position, ces différences s&#39;ils sont jugés en fonction de la taille de la différence (c. tailles d&#39;effet) pourraient conduire à s&#39;interroger sur la signification de ces différences. <img alt="Figure 3" fo:content-width="5in" src="/files/ftp_upload/50977/50977fig3highres.jpg" width="500" /> Figure 3. Résultantes de forces de réaction communes de la cheville, du genou, de la hanche et dans le antéropostérieur (panneaux de gauche) et les directions verticale (panneaux de droite). Données ont été moyennées sur des sujets de présentation. La phase d&#39;appui commence à 0% du cycle de la marche avec le contact du pied et se termine à environ 60% du cycle de marche avec décollage des orteils. Balançoire continue jusqu&#39;à ce que le prochain contact du pied de til même jambe à 100% du cycle de marche. <a href="https://www.jove.com/files/ftp_upload/50977/50977fig3highres.jpg" target="_blank">S&#39;il vous plaît cliquer ici pour voir une version plus grande de cette figure.</a> <img alt="Figure 4" fo:content-width="5in" src="/files/ftp_upload/50977/50977fig4highres.jpg" width="500" /> Figure 4. Des moments communs résultantes autour d&#39;un axe transversal (aka, axe médio-latérale) à travers la cheville, le genou et la hanche. Données ont été moyennées sur des sujets de présentation. La phase d&#39;appui commence à 0% du cycle de la marche avec le contact du pied et se termine à environ 60% du cycle de marche avec décollage des orteils. Balançoire poursuit jusqu&#39;à ce que le prochain contact de pied de la même jambe à 100% du cycle de marche. <img alt="Tableau 2" fo:content-width="6in" src="/files/ftp_upload/50977/50977table2.jpg" width="600" /> Tableau 2. Pic réaction commune résultantforces et des moments en moyenne dans toutes les disciplines et les comparaisons statistiques entre les deux modèles d&#39;inertie pour la cinétique communes de la prothèse secondaires. Notes: données moyennes sont présentés en moyenne (SD). % Colonne Gait Cycle représente le pourcentage moyen dans toutes les disciplines où la valeur de crête est survenu pour cette variable. P &lt;0,05 considéré comme significatif.

Watch this Scientific Journal Video about Oscillation and Reaction Board Techniques for Estimating Inertial Properties of a Below-knee Prosthesis at JoVE.com

Oscillation and Reaction Board Techniques for Estimating Inertial Properties of a Below-knee Prosthesis

segmentaires du corps les propriétés d&#39;inertie sont nécessaires pour la modélisation dynamique inverse. Utilisation d&#39;une oscillation et technique du conseil d&#39;administration de la réaction, les propriétés d&#39;inertie des prothèses-dessous du genou ont été mesurées. Utilisation des mesures directes de l&#39;inertie de la prothèse dans le modèle de la prothèse de jambe de dynamique inverse a donné lieu à des amplitudes inférieures des forces et moments résultants conjointes.

Oscillation et du Conseil de réaction des techniques d&#39;estimation inertie propriétés d&#39;une prothèse tibiale

The purpose of this study was two-fold: 1) demonstrate a technique that can be used to directly estimate the inertial properties of a below-knee ...

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Unit 1

Moment of Inertia

Oscillations

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16.6K vues.  University of Northern Colorado.  segmentaires du corps les propriétés d'inertie sont nécessaires pour la modélisation dynamique inverse. Utilisation d'une oscillation et technique du conseil d'administration de la réaction, les propriétés d'inertie des prothèses-dessous du genou ont été mesurées. Utilisation des mesures directes de l'inertie de la prothèse dans le modèle de la prothèse de jambe de dynamique inverse a donné lieu à des amplitudes inférieures des forces...

Vidéo: Oscillation and Reaction Board Techniques for Estimating Inertial Properties of a Below-knee Prosthesis

Measuring the Mechanical Properties of Living Cells Using Atomic Force Microscopy

Mechanical properties of cells and extracellular matrix (ECM) play important roles in many biological processes including stem cell differentiation, tumor formation, and wound healing. Changes in stiffness of cells and ECM are often signs of changes in cell physiology or diseases in tissues. Hence, cell stiffness is an index to evaluate the status of cell cultures. Among the multitude of methods applied to measure the stiffness of cells and tissues, micro-indentation using an Atomic Force Microscope (AFM) provides a way to reliably measure the stiffness of living cells. This method has been widely applied to characterize the micro-scale stiffness for a variety of materials ranging from metal surfaces to soft biological tissues and cells. The basic principle of this method is to indent a cell with an AFM tip of selected geometry and measure the applied force from the bending of the AFM cantilever. Fitting the force-indentation curve to the Hertz model for the corresponding tip geometry can give quantitative measurements of material stiffness. This paper demonstrates the procedure to characterize the stiffness of living cells using AFM. Key steps including the process of AFM calibration, force-curve acquisition, and data analysis using a MATLAB routine are demonstrated. Limitations of this method are also discussed.

This paper demonstrates a protocol to characterize the mechanical properties of living cells by means of microindentation using an Atomic Force Microscope (AFM).

Mesurer les propriétés mécaniques des cellules vivantes par microscopie à force atomique

Mechanical  properties of cells and extracellular matrix (ECM) play important roles in many  biological processes including stem cell differentiation, ...

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Bio-ingénierie

Engineering Platform and Experimental Protocol for Design and Evaluation of a Neurally-controlled Powered Transfemoral Prosthesis

To enable intuitive operation of powered artificial legs, an interface between user and prosthesis that can recognize the user's movement intent is desired. A novel neural-machine interface (NMI) based on neuromuscular-mechanical fusion developed in our previous study has demonstrated a great potential to accurately identify the intended movement of transfemoral amputees. However, this interface has not yet been integrated with a powered prosthetic leg for true neural control. This study aimed to report (1) a flexible platform to implement and optimize neural control of powered lower limb prosthesis and (2) an experimental setup and protocol to evaluate neural prosthesis control on patients with lower limb amputations. First a platform based on a PC and a visual programming environment were developed to implement the prosthesis control algorithms, including NMI training algorithm, NMI online testing algorithm, and intrinsic control algorithm. To demonstrate the function of this platform, in this study the NMI based on neuromuscular-mechanical fusion was hierarchically integrated with intrinsic control of a prototypical transfemoral prosthesis. One patient with a unilateral transfemoral amputation was recruited to evaluate our implemented neural controller when performing activities, such as standing, level-ground walking, ramp ascent, and ramp descent continuously in the laboratory. A novel experimental setup and protocol were developed in order to test the new prosthesis control safely and efficiently. The presented proof-of-concept platform and experimental setup and protocol could aid the future development and application of neurally-controlled powered artificial legs.

Neural-machine interfaces (NMI) have been developed to identify the user's locomotion mode. These NMIs are potentially useful for neural control of powered artificial legs, but have not been fully demonstrated. This paper presented (1) our designed engineering platform for easy implementation and development of neural control for powered lower limb prostheses and (2) an experimental setup and protocol in a laboratory environment to evaluate neurally-controlled artificial legs on patients with lower limb amputations safely and efficiently.

Plate-forme d&#39;ingénierie et de protocole expérimental pour la conception et l&#39;évaluation d&#39;un Propulsé Transfemoral Prothèse Neurally contrôlée

To enable intuitive operation of powered artificial legs, an interface between user and prosthesis that can recognize the user's movement intent is ...

In Situ Mapping of the Mechanical Properties of Biofilms by Particle-tracking Microrheology

Bacterial cells are able to form surface-attached biofilm communities known as biofilms by encasing themselves in extracellular polymeric substances (EPS). The EPS serves as a physical and protective scaffold that houses the bacterial cells and consists of a variety of materials that includes proteins, exopolysaccharides and DNA. The composition of the EPS may change, which remodels the mechanic properties of the biofilm to further develop or support alternative biofilm structures, such as streamers, as a response to environmental cues. Despite this, there are little quantitative descriptions on how EPS components contribute to the mechanical properties and function of biofilms. Rheology, the study of the flow of matter, is of particular relevance to biofilms as many biofilms grow in flow conditions and are constantly exposed to shear stress. It also provides measurement and insight on the spreading of the biofilm on a surface. Here, particle-tracking microrheology is used to examine the viscoelasticity and effective crosslinking roles of different matrix components in various parts of the biofilm during development. This approach allows researchers to measure mechanic properties of biofilms at the micro-scale, which might provide useful information for controlling and engineering biofilms.

In Situ Mapping of the Mechanical Properties of Biofilms by Particle-tracking Microrheology

Particle-tracking microrheology investigates the viscoelasticity of materials. Here, the technique is used to determine the viscoelasticity, creep compliance and effective crosslinking roles of different matrix components of a bacterial biofilm. The matrix consists of polymeric substances secreted by the bacteria and its components determine biofilm structure and mechanical properties.

En cartographie in situ des propriétés mécaniques des biofilms par Microrhéologie de particules de suivi

Bacterial cells are able to form surface-attached biofilm communities known as biofilms by encasing themselves in extracellular polymeric substances ...

Techniques for the Evolution of Robust Pentose-fermenting Yeast for Bioconversion of Lignocellulose to Ethanol

Lignocellulosic biomass is an abundant, renewable feedstock useful for production of fuel-grade ethanol and other bio-products. Pretreatment and enzyme saccharification processes release sugars that can be fermented by yeast. Traditional industrial yeasts do not ferment xylose (comprising up to 40% of plant sugars) and are not able to function in concentrated hydrolyzates. Concentrated hydrolyzates are needed to support economical ethanol recovery, but they are laden with toxic byproducts generated during pretreatment. While detoxification methods can render hydrolyzates fermentable, they are costly and generate waste disposal liabilities. Here, adaptive evolution and isolation techniques are described and demonstrated to yield derivatives of the native Scheffersomyces stipitis strain NRRL Y-7124 that are able to efficiently convert hydrolyzates to economically recoverable ethanol despite adverse culture conditions. Improved individuals are enriched in an evolving population using multiple selection pressures reliant on natural genetic diversity of the S. stipitis population and mutations induced by exposures to two diverse hydrolyzates, ethanol or UV radiation. Final evolution cultures are dilution plated to harvest predominant isolates, while intermediate populations, frozen in glycerol at various stages of evolution, are enriched on selective media using appropriate stress gradients to recover most promising isolates through dilution plating. Isolates are screened on various hydrolyzate types and ranked using a novel procedure involving dimensionless relative performance index (RPI) transformations of the xylose uptake rate and ethanol yield data. Using the RPI statistical parameter, an overall relative performance average is calculated to rank isolates based on multiple factors, including culture conditions (varying in nutrients and inhibitors) and kinetic characteristics. Through application of these techniques, derivatives of the parent strain had the following improved features in enzyme saccharified hydrolyzates at pH 5-6: reduced initial lag phase preceding growth, reduced diauxic lag during glucose-xylose transition, significantly enhanced fermentation rates, improved ethanol tolerance and accumulation to 40 g/L.

Adaptive evolution and isolation techniques are described and demonstrated to yield derivatives of Scheffersomyces stipitis strain NRRL Y-7124 that are able to rapidly consume hexose and pentose mixed sugars in enzyme saccharified undetoxified hydrolyzates and to accumulate over 40 g/L ethanol.

Techniques pour l&#39;évolution de la levure robuste Pentose-fermentation pour la bioconversion de lignocellulose en éthanol

Lignocellulosic biomass is an abundant, renewable feedstock useful for production of fuel-grade ethanol and other bio-products. Pretreatment and enzyme ...

Production of Metal Nanoparticles by Pulsed Laser-ablation in Liquids: A Tool for Studying the Antibacterial Properties of Nanoparticles

The emergence of multidrug-resistant bacteria is a global clinical concern leading some to speculate about our return to a "pre-antibiotics" era of medicine. In addition to efforts to identify novel small-molecule antimicrobial drugs, there has been great interest in the use of metal nanoparticles as coatings for medical devices, wound dressings, and consumer packaging, due to their antimicrobial properties. The wide variety of methods available for nanoparticle synthesis results in a broad spectrum of chemical and physical properties which can affect antibacterial efficacy. This manuscript describes the pulsed laser-ablation in liquids (PLAL) method to create nanoparticles. This approach allows for the fine tuning of nanoparticle size, composition, and stability using post-irradiation methods as well as the addition of surfactants or volume excluders. By controlling particle size and composition, a large range of physical and chemical properties of metal nanoparticles can be explored which may contribute to their antimicrobial efficacy thereby opening new avenues for antibacterial development.

The antimicrobial properties of metals such as copper and silver have been recognized for centuries. This protocol describes pulsed laser-ablation in liquids, a method of synthesizing metal nanoparticles that provides the ability to fine tune the properties of these nanoparticles to optimize their antimicrobial effects.

Production de nanoparticules métalliques par laser-ablation pulsée dans les liquides: un outil pour étudier les propriétés antibactériennes des nanoparticules

The emergence of multidrug-resistant bacteria is a global clinical concern leading some to speculate about our return to a "pre-antibiotics" era of ...

Synthesis of Hydrogels with Antifouling Properties As Membranes for Water Purification

Hydrogels have been widely utilized to enhance the surface hydrophilicity of membranes for water purification, increasing the antifouling properties and thus achieving stable water permeability through membranes over time. Here, we report a facile method to prepare hydrogels based on zwitterions for membrane applications. Freestanding films can be prepared from sulfobetaine methacrylate (SBMA) with a crosslinker of poly(ethylene glycol) diacrylate (PEGDA) via photopolymerization. The hydrogels can also be prepared by impregnation into hydrophobic porous supports to enhance the mechanical strength. These films can be characterized by attenuated total reflection Fourier transform infrared spectroscopy (ATR-FTIR) to determine the degree of conversion of the (meth)acrylate groups, using goniometers for hydrophilicity and differential scanning calorimetry (DSC) for polymer chain dynamics. We also report protocols to determine the water permeability in dead-end filtration systems and the effect of foulants (bovine serum albumin, BSA) on membrane performance.

This paper reports practical methods to prepare hydrogels in freestanding films and impregnated membranes and to characterize their physical properties, including water transport properties.

Synthèse des hydrogels avec des propriétés antisalissure Membranes pour la purification de l&#39;eau

Hydrogels have been widely utilized to enhance the surface hydrophilicity of membranes for water purification, increasing the antifouling properties and ...

Semiautomated Longitudinal Microcomputed Tomography-based Quantitative Structural Analysis of a Nude Rat Osteoporosis-related Vertebral Fracture Model

Osteoporosis-related vertebral compression fractures (OVCFs) are a common and clinically unmet need with increasing prevalence as the world population ages. Animal OVCF models are essential to the preclinical development of translational tissue engineering strategies. While a number of models currently exist, this protocol describes an optimized method for inducing multiple highly reproducible vertebral defects in a single nude rat. A novel longitudinal semiautomated microcomputed tomography (&#181;CT)-based quantitative structural analysis of the vertebral defects is also detailed. Briefly, rats were imaged at multiple time points post-op. The day 1 scan was reoriented to a standard position, and a standard volume of interest was defined. Subsequent &#181;CT scans of each rat were automatically registered to the day 1 scan so the same volume of interest was then analyzed to assess for new bone formation. This versatile approach can be adapted to a variety of other models where longitudinal imaging-based analysis could benefit from precise 3D semiautomated alignment. Taken together, this protocol describes a readily quantifiable and easily reproducible system for osteoporosis and bone research. The suggested protocol takes 4 months to induce osteoporosis in nude ovariectomized rats and between 2.7 and 4 h to generate, image, and analyze two vertebral defects, depending on tissue size and equipment.

The goal of this protocol is to generate a nude rat osteoporosis-related vertebral compression fracture model that can be longitudinally evaluated in vivo using a semiautomated microcomputed tomography-based quantitative structural analysis.

Semi-automatisées longitudinale axée sur les Microcomputed tomographie Quantitative analyse structurale d’un modèle de Rat nu Fracture vertébrale liée à l’ostéoporose

Osteoporosis-related vertebral compression fractures (OVCFs) are a common and clinically unmet need with increasing prevalence as the world population ...

A Millimeter Scale Flexural Testing System for Measuring the Mechanical Properties of Marine Sponge Spicules

Many load bearing biological structures (LBBSs)&#8212;such as feather rachises and spicules&#8212;are small (&#60;1 mm) but not microscopic. Measuring the flexural behavior of these LBBSs is important for understanding the origins of their remarkable mechanical functions.
We describe a protocol for performing three-point bending tests using a custom-built mechanical testing device that can measure forces ranging from 10-5 to 101 N and displacements ranging from 10-7 to 10-2 m. The primary advantage of this mechanical testing device is that the force and displacement capacities can be easily adjusted for different LBBSs. The device&#39;s operating principle is similar to that of an atomic force microscope. Namely, force is applied to the LBBS by a load point that is attached to the end of a cantilever. The load point displacement is measured by a fiber optic displacement sensor and converted into a force using the measured cantilever stiffness. The device&#39;s force range can be adjusted by using cantilevers of different stiffnesses.
The device&#39;s capabilities are demonstrated by performing three-point bending tests on the skeletal elements of the marine sponge Euplectella aspergillum. The skeletal elements&#8212;known as spicules&#8212;are silica fibers that are approximately 50 &#181;m in diameter. We describe the procedures for calibrating the mechanical testing device, mounting the spicules on a three-point bending fixture with a &#8776;1.3 mm span, and performing a bending test. The force applied to the spicule and its deflection at the location of the applied force are measured.

We present a protocol for performing three-point bending tests on sub-millimeter scale fibers using a custom-built mechanical testing device. The device can measure forces ranging from 20 &#181;N up to 10 N and can therefore accommodate a variety of fiber sizes.

Un système de test en flexion millimètre pour mesurer les propriétés mécaniques des Spicules d’éponges marines

Many load bearing biological structures (LBBSs)&#8212;such as feather rachises and spicules&#8212;are small (&#60;1 mm) but not microscopic. Measuring the ...

Synthesis of Multi-walled Carbon Nanotubes Modified with Silver Nanoparticles and Evaluation of Their Antibacterial Activities and Cytotoxic Properties

In this study, multi-walled carbon nanotubes (MWCNTs) were treated with an aqueous sulfuric acid solution to form an oxygen-based functional group. Silver MWCNTs were prepared by the reductive deposition of silver from an aqueous solution of AgNO3 on the oxidized MWCNTs. Given the unique color of the CNTs, it was not possible to apply them to the minimum inhibitory concentration or mitochondrial toxicity assays to evaluate the toxicity and antibacterial properties, since they would interfere with the assays. The inhibition zone and minimum bactericidal concentration for the Ag-MWCNTs were measured and Live/Dead and Trypan Blue assays were used to measure the toxicity and antibacterial properties without interfering with the color of the CNTs.

In this study, antimicrobial nanomaterials were synthesized by acidic oxidation of multiwalled carbon nanotubes and subsequent reductive deposition of silver nanoparticles. Antimicrobial activity and cytotoxicity tests were performed with the as-prepared nanomaterials.

Synthèse des Nanotubes de carbone Multi modifiés avec des nanoparticules d’argent et de l’évaluation de leurs activités antibactériennes et propriétés cytotoxiques

In this study, multi-walled carbon nanotubes (MWCNTs) were treated with an aqueous sulfuric acid solution to form an oxygen-based functional group. Silver ...

3D Printing of In Vitro Hydrogel Microcarriers by Alternating Viscous-Inertial Force Jetting

Microcarriers are beads with a diameter of 60-250 &#181;m and a large specific surface area, which are commonly used as carriers for large-scale cell cultures. Microcarrier culture technology has become one of the main techniques in cytological research and is commonly used in the field of large-scale cell expansion. Microcarriers have also been shown to play an increasingly important role in in vitro tissue engineering construction and clinical drug screening. Current methods for preparing microcarriers include microfluidic chips and inkjet printing, which often rely on complex flow channel design, an incompatible two-phase interface, and a fixed nozzle shape. These methods face the challenges of complex nozzle processing, inconvenient nozzle changes, and excessive extrusion forces when applied to multiple bioink. In this study, a 3D printing technique, called alternating viscous-inertial force jetting, was applied to enable the construction of hydrogel microcarriers with a diameter of 100-300 &#181;m. Cells were subsequently seeded on microcarriers to form tissue engineering modules. Compared to existing methods, this method offers a free nozzle tip diameter, flexible nozzle switching, free control of printing parameters, and mild printing conditions for a wide range of bioactive materials.

3D Printing of In Vitro Hydrogel Microcarriers by Alternating Viscous-Inertial Force Jetting

Presented here is a mild 3D printing technique driven by alternating viscous-inertial forces to enable the construction of hydrogel microcarriers. Homemade nozzles offer flexibility, allowing easy replacement for different materials and diameters. Cell binding microcarriers with a diameter of 50-500 &#181;m can be obtained and collected for further culturing.

Impression 3D de microporteurs d’hydrogel in vitro par jet de force visqueuse-inertielle alternée

Microcarriers are beads with a diameter of 60-250 &#181;m and a large specific surface area, which are commonly used as carriers for large-scale cell ...