Los autores desean agradecer a Gabriel Arom y Michael Yeranosian por sus contribuciones técnicas a las iteraciones anteriores de este proyecto. Este proyecto fue financiado por el OREF Clínico Científico Training Grant (NL), HH Lee quirúrgica Beca de Investigación (NL), la Administración de Veteranos BLR + D Revisión Mérito 1 I01 BX00012601 (DM) y Musculoesqueléticas Trasplante Fundación Premio al Investigador Joven (FP).

NOTA: Todas las cirugías animales fueron aprobadas por el personal y animal veterinaria comité uso local antes de comenzar los experimentos. 1. Preparación de electrohiladas policaprolactona Andamios <ol><li> Pesar y disolver éster de grado médico terminado poli (ε-caprolactona) en forma de gránulos en 1,1,1,3,3,3-hexafluoro-2-propanol para crear un 10% w / w solución del polímero PCL. Deje que el revuelo solución utilizando una placa de agitación durante al menos 3 horas para asegurar una solución homogénea. </li><li> Electrospin la solución PCL para crear un brazalete de fibras PCL altamente alineados para la fabricación de andamios. <ol><li> Preparar la instalación electrospinning en una campana de extracción química con el ventilador encendido en todo momento. Este consiste en una caja de acrílico grande que servirá como un medio de vacío aislado para el proceso de electrospinning y tiene puntos de entrada para la solución de fuente PCL impulsado por una fuente de tensión, el mandril recogiendo accionado por motor, y un puerto de vacío. Limpie el Acrylicaja de c a fondo con etanol y cubre todas las superficies con hojas de Parafilm para eliminar las impurezas que puedan comprometer la calidad del producto electrospun. </li><li> Cargar aproximadamente 3 ml de la solución anterior en una jeringa de 10 ml con un objeto contundente terminaron 18 G, la aguja 1 ½ pulgadas. Quite las burbujas de aire empujando la jeringa hacia arriba. Solución de bloqueo en una bomba de inyección programable. Insertar la aguja a través de un pequeño agujero en la caja de acrílico, dejando alrededor de ½ pulgada de la aguja fuera de la caja de acrílico para la fijación del cable de la fuente de tensión. </li><li> Use un 30 mm girando mandril del torno como el colector para las fibras PCL altamente alineados; cubrir el mandril firmemente con una tira delgada de papel de aluminio. Bloquear el mandril en el motor en el lado opuesto de la caja de unos 15 cm de distancia de la aguja de la jeringa. </li><li> Inserte la manguera de plástico en el puerto de vacío y conectarse a la fuente de vacío campana de humos. Encienda la fuente de vacío y para abarcar la caja de acrílico con una tapa. </li><li> Set la velocidad de infusión de la bomba de jeringa programable a 2,5 ml / hr. Encienda el motor para operar en el mandril a 3.450 rpm y conecte el cable positivo de la fuente de tensión a la punta de la aguja fuera de la caja con una pinza. </li><li> Una vez que la infusión de la solución PCL ha comenzado, encienda la fuente de tensión y establecer a una tensión de servicio de 20 kV. </li><li> Infundir la solución durante 12 minutos para crear un manguito homogénea de 0,5 ml de la solución de PCL. NOTA: En promedio, cada manguito tiene suficiente material de electrospun para crear dos hojas de seis tiras, que pueden ser utilizados para crear un total de tres andamios de cuatro capas. </li></ol></li><li> Láser cortar el manguito PCL para formar múltiples pequeñas hojas en un VersaLaser Cortador 2.3 operada en el ajuste bajo vacío, el voltaje de aterrizaje 10,0 keV, distancia de trabajo 6,4 mm, y el diámetro de la sonda de 3,0. NOTA: En este ejemplo, un diseño asistido por ordenador se utiliza para instruir a la cuchilla para producir varias hojas de 1,5 mm x 35 mm x 150 micras con andamiosdistribuido uniformemente 150 micras de diámetro en un 15% el área de poro. </li><li> Plasma etch los andamios PCL utilizando un limpiador de plasma para inducir la hidrofilia de la superficie PCL con aceleración de iones. Ajuste el vacío a 450 Pa y la delicia de los andamios durante 30 segundos a alta potencia (29,6 W). </li><li> Bañar los andamios en etanol al 70% en un ambiente estéril. </li><li> Escudo los andamios individuales con colágeno para facilitar la adhesión y proliferación celular in vivo. <ol><li> Crear una solución de recubrimiento de colágeno mediante la dilución de un 8: solución estéril de 2,5 Purecol colágeno 3 mg / ml de solución patrón, 10x PBS y 0,1 N NaOH 1:: 1 9 en 1X PBS a 4 ° C. Mezclar bien para asegurar la homogeneidad solución. </li><li> Escudo individuo 1,5 mm x 35 mm x 150 micras andamios con una película fina capa de la solución de colágeno anteriormente. Deje secar durante 24 horas en un ambiente estéril. </li></ol></li><li> El uso de suturas de Vicryl 5-0, apilar y colocar cuatro individuo 1,5 mm x 35 mm x 150 micras andamiosutilizando un Krackow puntada para crear un final 0,6 mm de espesor de capas múltiples, andamios, revestida de colágeno que está listo para su implantación. </li></ol> 2. Protocolo de Cirugía de la rata <ol><li> Inducir la anestesia mediante la colocación de la rata en la cámara de inhalación y la entrega de 2% de isoflurano con 2 L / min de oxígeno. Confirmar la rata se anestesia adecuada por aplicación de presión a las patas traseras y la evaluación de cualquier respuesta. </li><li> Sobre la mesa de vuelta no estériles, por vía subcutánea inyectar 25 mg / kg de ampicilina y 0,03 mg / kg de buprenorfina. </li><li> Aplique un ungüento oftálmico para los ojos. Clip de la piel de la extremidad posterior operativa y preparar la zona quirúrgica con tres matorrales alternas de clorhexidina y etanol al 70%. </li><li> Traslado a la rata a la mesa de operaciones, en un cojín con calefacción para evitar la hipotermia. Secure nariz cono, y mantener la anestesia a través del procedimiento con un 2% de isoflurano en 2 l / min de oxígeno, cono de la nariz entregado. Coloque de una manera estéril, dejando la extremidad operativa expuesta. </li><li&gt; Antes de comenzar la cirugía, primero confirmar anestesia adecuada por la falta de una respuesta a la presión del pie traseras. </li><li> Hacer un 2 cm de largo medial incisión vertical a la rodilla, centrado en el nivel de la rótula. Retraer la piel lateralmente hasta que la incisión se centra sobre la rodilla. </li><li> Utilice un bisturí para realizar una artrotomía parapatelar medial cortando justo medial a la rótula y que se extiende proximalmente hasta el nivel de la unión musculotendinosa de los cuádriceps y distalmente al nivel de la inserción del tendón rotuliano en el tubérculo tibial. Tenga cuidado de no cortar los rotulianos o cuádriceps tendones. </li><li> Rótula Release lateralmente haciendo una incisión vertical de 1 cm a través de la cápsula de la rodilla justo lateral al tendón patelar. </li><li> Asegúrese de que la rodilla está extendida. Tome un par de tijeras finas y pasar por debajo de la rótula de lateral a medial. Difundir las tijeras un par de veces para que el mecanismo extensor se puede traducir a cualquier lado. </li><li> Mientras flexionando tél la rodilla, traducir la rótula lateralmente para exponer el interior de la articulación de la rodilla. Asegurar una visualización clara de la escotadura intercondílea y cóndilos femorales. El uso de un bisturí, seccionar la ACL y PCL en la muesca. </li><li> Taladro eléctrico de carga con un alambre de Kirschner de 1,6 mm. Coloque la punta de Kirschner en el origen del LCA en la escotadura intercondílea. Perforar superolateralmente y visualizar el punto de salida en la cara lateral del fémur, la eliminación de cualquier tejido suave como sea necesario con un bisturí. Pase el alambre de Kirschner y salir un par de veces para asegurarse de paso libre para el injerto. </li><li> Coloque el alambre de Kirschner en la huella de ACL en la meseta tibial. Perforar anterolateralmente y visualizar punto de salida en la tibia proximal anterolateral. Utilice bisturí para limpiar el tejido blando como sea necesario para que el punto donde el k-alambre sale de la tibia está totalmente visualizada. </li><li> Pasar una aguja Keith acortada (idealmente no más de 2 pulgadas de largo) a través del túnel del hueso femoral. Pase los dos extremos de la sutura de un extremo del injerto a través del ojo de la Kaguja eith. Utilice la aguja para tirar de un extremo del injerto a través del túnel femoral. </li><li> Repita el paso antes de pasar el otro extremo del injerto a través del túnel tibial. </li><li> Utilice 4-0 Vicryl sutura para fijar el extremo femoral del injerto al que rodea periostio u otro tejido blando con una puntada figura en forma de ocho. Manual de la tensión del injerto con la rodilla en extensión. Asegurar el extremo tibial del injerto al que rodea periostio u otro tejido blando con una puntada figura en forma de ocho. </li><li> Utilice una tijera para cortar el exceso de injerto en ambos extremos, dejando 1-2 mm en cada extremo pasado la puntada figura en forma de ocho. </li><li> Extender la rodilla y reducir la rótula. Utilizando 4-0 vicryl, coloque una sola puntada figura en forma de ocho para cerrar la cápsula articular medial, evitando subluxación lateral de la rótula. </li><li> Cierre la piel con una subcuticular 5-0 Monocryl o Vicryl sutura continua, con cuidado de no suturar el músculo subyacente o tiene cualquier sutura visible una vez que la piel se cierra. </li><li> Inject ratas por vía subcutánea con buprenorfina cada 12 hr para un total de tres días después de la operación. Visite el sitio quirúrgico para cualquier secreción o dehiscencia de la herida en el momento de la inyección. Cojeando y un poco de hinchazón son normales en los primeros días después de la cirugía, pero prontamente abordar cualquier preocupación postoperatorias en conjunto con el personal veterinario. El animal puede ser de vuelta a la vivienda social a las 2 semanas después de la operación, cuando las incisiones quirúrgicas hayan desaparecido por completo. </li></ol> 3. Protocolo de Recolección de Datos <ol><li> En el momento del sacrificio, asfixiar ratas individualmente en una cámara cerrada CO 2 seguido por toracotomía. </li><li> Cosecha tanto las extremidades reconstruidas quirúrgicamente y contralateral separando en la articulación de la cadera. <ol><li> Para las extremidades reconstruidas, eliminar todo el tejido blando, incluyendo el ligamento cruzado posterior y los restos de la ACL nativo alterado quirúrgicamente, mediante disección fina para aislar sólo el fémur, la tibia, y el injerto. </li> &lt;li&gt; En las extremidades contralaterales, eliminar todo el tejido blando, excepto la ACL nativo, así como el fémur y la tibia por la disección fina. </li><li> Utilice una herramienta rotativa, tales como Dremel, para eliminar todo pero ¾ a 1 cm de hueso de cada extremo del complejo fémur-injerto tibia. </li><li> Durante este proceso ya lo largo de las pruebas biomecánicas, con regularidad y frecuencia rocíe las regiones ligamentosas con solución salina normal para evitar la desecación de la rodilla cosechado que pueden alterar los resultados falsamente. </li></ol></li><li> Para el análisis histológico, fijar cada rodilla individualmente en solución de paraformaldehído al 4% a 25 ° C durante 48 hr. A continuación, sumergir la rodilla en una solución de Immunocal reactivo para la descalcificación completa; este proceso depende de los contenidos calcificación de la muestra y puede tomar hasta cinco días. Compruebe muestras individuales diaria para evaluar el progreso como la descalcificación incompleta puede disminuir la calidad de la muestra. Una vez completa, realice el corte, tobogán de montaje, y la tinción si lo deseas. </li><li> Perform pruebas biomecánicas para evaluar la capacidad funcional de la ingeniería tisular ligamento. <ol><li> Asegurar el fémur y la tibia envolviendo 28 G alambre de acero galvanizado alrededor de la epífisis de cada hueso separado. Esto es para evitar que los datos de pruebas biomecánicas inexactas de fallo prematuro de la tracción de la muestra en el hueso en lugar de en el ligamento de interés. </li><li> Pot el fémur en una mezcla de cemento de polimetilmetacrilato (PMMA) de hueso. Para ello, mezclar los dos componentes del cemento y utilizar inmediatamente la mezcla viscosa para asegurar el fémur en el metal, que encierra completamente la diáfisis del hueso en la olla cementada con la epífisis y el ligamento adjunto que sobresale libremente. Permitir la polimerización de radicales libres espontánea para transformar gradualmente los componentes viscosos mixtos a un material pastoso y, finalmente, en una matriz endurecida sólido. NOTA: Este proceso tarda varios minutos y se puede controlar manualmente mediante la evaluación de la temperatura de un bolo a partir deel cemento restante; la temperatura debe aumentar transitoriamente durante la reacción de polimerización exotérmica y disminuir a RT después el material se solidifica. </li><li> Repita el mismo proceso anterior para cementar la tibia, excepto la vez que mantiene el ligamento de la rodilla en 20 ° de flexión para la prueba mecánica ideal. </li><li> Montar el complejo fémur-injerto tibia cementado en un aparato de ensayo de tracción, y preparar a la carga de registro y el desplazamiento como una función de tiempo desde el comienzo de la tensión al fracaso. En este ejemplo, se utilizó un modelo Instron 5564 con una célula de carga de 1 kN. </li><li> Pre-tensión del injerto a 2 N a una velocidad de rampa de 0,5 N / min y luego probar el injerto al fracaso a una velocidad de deformación de 0,5 mm / seg. Durante el proceso, asegúrese de que el ligamento está fallando en la mitad de la sustancia y que el fémur y la tibia ósea son seguras y no prematuramente en su defecto, que puede evaluar de manera inexacta propiedades biomecánicas del ligamento probado. </li><li> Utilice el desplazamiento de carga generadacurvas para calcular la carga de rotura y la rigidez del ligamento probado. </li></ol></li></ol>

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C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=In+vivo+study+of+anterior+cruciate+ligament+regeneration+using+mesenchymal+stem+cells+and+silk+scaffold.">In vivo study of anterior cruciate ligament regeneration using mesenchymal stem cells and silk scaffold.</a> Biomaterials. 29 (23), 3324-3337 (2008).</li><li>Landis, J. R., Koch, G. G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+measurement+of+observer+agreement+for+categorical+data.">The measurement of observer agreement for categorical data.</a> Biometrics. 33 (1), 159-174 (1977).</li><li>Joshi, S. M., Mastrangelo, A. N., Magarian, E. M., Fleming, B. C., Murray, M. M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Collagen-platelet+composite+enhances+biomechanical+and+histologic+healing+of+the+porcine+anterior+cruciate+ligament.">Collagen-platelet composite enhances biomechanical and histologic healing of the porcine anterior cruciate ligament.</a> Am J Sports Med. 37 (12), 2401-2410 (2009).</li><li>Leong, N. L., 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=In+vitro+and+in+vivo+evaluation+of+heparin+mediated+growth+factor+release+from+tissue-engineered+constructs+for+anterior+cruciate+ligament+reconstruction.">In vitro and in vivo evaluation of heparin mediated growth factor release from tissue-engineered constructs for anterior cruciate ligament reconstruction.</a> J Orthop Res. 10, (2014).</li><li>Seo, Y. K., 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=Increase+in+cell+migration+and+angiogenesis+in+a+composite+silk+scaffold+for+tissue-engineered+ligaments.">Increase in cell migration and angiogenesis in a composite silk scaffold for tissue-engineered ligaments.</a> J Orthop Res. 27 (4), 495-503 (2009).</li><li>Freeman, J. W., Woods, M. D., Laurencin, C. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Tissue+engineering+of+the+anterior+cruciate+ligament+using+a+braid-twist+scaffold+design.">Tissue engineering of the anterior cruciate ligament using a braid-twist scaffold design.</a> J Biomech. 40 (9), 2029-2036 (2007).</li><li>Bashur, C. A., Shaffer, R. D., Dahlgren, L. A., Guelcher, S. A., Goldstein, A. S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Effect+of+fiber+diameter+and+alignment+of+electrospun+polyurethane+meshes+on+mesenchymal+progenitor+cells.">Effect of fiber diameter and alignment of electrospun polyurethane meshes on mesenchymal progenitor cells.</a> Tissue Eng Part A. 15 (9), 2435-2445 (2009).</li><li>Dash, T. K., Konkimalla, V. B. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Poly-&#1108;-caprolactone+based+formulations+for+drug+delivery+and+tissue+engineering:+A+review.">Poly-&#1108;-caprolactone based formulations for drug delivery and tissue engineering: A review.</a> J Control Release. 158 (1), 15-33 (2012).</li><li>Yoshimoto, H., Shin, Y. M., Terai, H., Vacanti, J. P. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+biodegradable+nanofiber+scaffold+by+electrospinning+and+its+potential+for+bone+tissue+engineering.">A biodegradable nanofiber scaffold by electrospinning and its potential for bone tissue engineering.</a> Biomaterials. 24 (12), 2077-2082 (2003).</li><li>Xu, Y., Ao, Y. F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Histological+and+biomechanical+studies+of+inter-strand+healing+in+four-strand+autograft+anterior+cruciate+ligament+reconstruction+in+a+rabbit+model.">Histological and biomechanical studies of inter-strand healing in four-strand autograft anterior cruciate ligament reconstruction in a rabbit model.</a> Knee Surg Sports Traumatol Arthrosc. 17 (7), 770-777 (2009).</li><li>Shino, K., 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=Replacement+of+the+anterior+cruciate+ligament+by+an+allogeneic+tendon+graft.+An+experimental+study+in+the+dog.">Replacement of the anterior cruciate ligament by an allogeneic tendon graft. An experimental study in the dog.</a> J Bone Joint Surg Br. 66 (5), 672-681 (1984).</li><li>Stasiak, M. E., 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=A+novel+device+to+apply+controlled+flexion+and+extension+to+the+rat+knee+following+anterior+cruciate+ligament+reconstruction.">A novel device to apply controlled flexion and extension to the rat knee following anterior cruciate ligament reconstruction.</a> J Biomech Eng. 134 (4), 041008 (2012).</li><li>Brophy, R. H., 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=Effect+of+short-duration+low-magnitude+cyclic+loading+versus+immobilization+on+tendon-bone+healing+after+ACL+reconstruction+in+a+rat+model.">Effect of short-duration low-magnitude cyclic loading versus immobilization on tendon-bone healing after ACL reconstruction in a rat model.</a> J Bone Joint Surg Am. 93 (4), 381-393 (2011).</li></ol>

The authors declare that they have no competing financial interests.

Las lesiones del LCA son una condición común en la cirugía ortopédica deportes, con opciones limitadas para la reconstrucción en la actualidad. A fin de desarrollar un sustituto de tejido de ingeniería apropiado para la ACL que permitirá la regeneración in vivo, se requiere un modelo animal adecuado. En este estudio, la fabricación de un injerto de ingeniería biodegradable se describe, como es su implantación in vivo utilizando un modelo reproducible de la reconstrucción del LCA en una rata...

La rotura del ligamento cruzado anterior (LCA) es una de las más comunes las lesiones de ligamentos de la rodilla 1. Debido a la rotura de ligamento cruzado anterior de es incapaz de curar sin intervención quirúrgica, las limitaciones en las actividades de la vida diaria, así como la participación en deportes en coche más de 175.000 pacientes a someterse a cirugía cada año 2, con un costo estimado de mil millones de dólares al año 3. En la actualidad, ya sea autoinjerto o aloinjerto de tendón se utiliza para la reconstrucción del ligamento. Aunque altas tasas de éxito se puede lograr tanto con autoinjerto y aloinjerto de reemplazo, las complicaciones graves se asocian con estas opciones de reconstrucción 4. Tejido autoinjerto se asocia con morbilidad del sitio donante y se limita la oferta, sobre todo en casos de re-ruptura o lesiones múltiples ligamentosa. Por otro lado, el tejido de aloinjerto está vinculado con la integración retardada del injerto, la respuesta inflamatoria adversa, el riesgo infeccioso teórico, y supl limitadaly 5. Injertos no degradables sintéticos fueron desarrollados en los años 1970 y 1980, pero se vieron obstaculizados por la ruptura prematura del injerto, reacción de cuerpo extraño, osteolisis, y sinovitis 6. Como resultado de estas graves preocupaciones, actualmente no hay injertos sintéticos disponibles para uso clínico en los Estados Unidos. Debido a estas limitaciones con opciones de injerto existentes y a la evolución reciente de la biología, la ingeniería y la medicina regenerativa, ha habido un gran interés en una solución de ingeniería de tejidos para ACL injerto. Las estrategias de ingeniería de tejidos actuales emplean materiales biológicos y sintéticos degradables para permitir el crecimiento de tejido anfitrión evitando al mismo tiempo las limitaciones asociadas con la implantación de material sintético permanente 7. La policaprolactona (PCL) es un polímero biodegradable que es aprobado por la FDA para un número de aplicaciones médicas, incluyendo barrera de adhesión y un vendaje de heridas 8, que ha sido used en una amplia variedad de aplicaciones, incluyendo vascular, hueso, cartílago, nervios, piel, y la ingeniería de tejido esofágico 5,9-16. Biocompatibilidad favorable, relativamente larga in vivo la vida media, una resistencia mecánica adecuada, alta elasticidad y contribuyen a la popularidad de este polímero en la ingeniería de tejidos. En un modelo de roedor de la cicatrización de heridas, implantado PCL electrospun ha demostrado ser no inmunogénica y de integrarse en el tejido local sin reacciones adversas 13. Una imagen SEM de electrospun PCL se muestra en la Figura 1. Con actual de la FDA reguladora normas, la eficacia y la seguridad tanto en modelos animales pequeños y grandes que se requeriría para un PCL o cualquier otro injerto de LCA diseñado para moverse en ensayos clínicos en los Estados Unidos. Además, las condiciones in vivo a menudo pueden aumentar las propiedades de un injerto de tejido in vitro de ingeniería. Un modelo de rata de la reconstrucción del LCA autólogo con digitor flexorum tendón del se ha descrito anteriormente, en el que se rompió el ligamento cruzado anterior nativa, femoral y tibial túneles fueron perforados, y el injerto fue aprobada y se fija mediante sutura 17-22. En este artículo, vamos a describir una modificación de este modelo para la evaluación de los reemplazos de ACL ingeniería en lugar de para la reconstrucción a base de autoinjerto (Figura 2). Aunque existen muchos modelos animales para la ingeniería de tejido del ligamento, la rata es ventajoso en comparación con los modelos más grandes para un número de razones. Estas ventajas incluyen la cría y manejo más fácil, menos consideraciones éticas, y la reducción de 17,23 costo. Además, el modelo de rata se ha usado extensivamente como un modelo para la regeneración de tejido ortopédico, incluyendo el cartílago, tendón, y la ingeniería de tejido óseo 24. En particular, las ratas desnudos atímicos se eligieron debido a su falta de respuesta inmune mediada por células 25, permitiendo la implantación eventual of células del donante xenogeneicos en este modelo para mejorar aún más el injerto de ingeniería en el futuro. En este documento métodos, se describe la fabricación y la implantación quirúrgica de un acelular, injerto de polímero biodegradable en un modelo de rata atímicos de reconstrucción del LCA.

<table border="0" cellpadding="0" cellspacing="0" width="888">
	<tbody>
		<tr height="34">
			<td height="34" style="height:34px;width:347px;">Name of Material/ Equipment</td>
			<td style="width:147px;">Company</td>
			<td style="width:77px;">Catalog Number</td>
			<td style="width:317px;">Comments/Description</td>
		</tr>
		<tr height="34">
			<td height="34" style="height:34px;width:347px;">Medical grade ester terminated poly (&#949;-caprolactone), granule form (MW = 110,000)</td>
			<td style="width:147px;">Lactel Absorbable Polymers</td>
			<td style="width:77px;"></td>
			<td style="width:317px;">Custom synthesized polymer to desired molecular weight</td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">1,1,1,3,3,3-hexafluoro-2-propanol</td>
			<td style="width:147px;">Sigma-Aldrich</td>
			<td>105228</td>
			<td style="width:317px;">Solvent for PCL polymer</td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">18G x 1 1/2&#34;bevel needle</td>
			<td style="width:147px;">BD Medical</td>
			<td>305196</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">Remote Infuse/Withdraw Programmable Syringe Pump</td>
			<td style="width:147px;">Harvard Apparatus</td>
			<td style="width:77px;">702101</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">VersaLaser VLS2.30 Laser Engraver</td>
			<td style="width:147px;">Microgeo USA</td>
			<td style="width:77px;">VLS2.30</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="34">
			<td height="34" style="height:34px;width:347px;">Expanded Plasma Cleaner 115V</td>
			<td style="width:147px;">Harrick Plasma</td>
			<td style="width:77px;">PDC-001</td>
			<td style="width:317px;">Plasma etch just prior to collagen coating for surface modification</td>
		</tr>
		<tr height="34">
			<td height="34" style="height:34px;width:347px;">PureCol&#160; Collagen Standard Solution, 3 mg/ml</td>
			<td style="width:147px;">Advanced Biomatrix</td>
			<td style="width:77px;">5015-A</td>
			<td style="width:317px;">Mix 8:1:2.5 solution of PureCol, 10x PBS, 0.1N NaOH 1:9 in 1x PBS</td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">Suture, 5-0 Vicryl</td>
			<td style="width:147px;">Henry Schein</td>
			<td style="width:77px;">1086471</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;">Suture, 4-0 Vicryl</td>
			<td style="width:147px;">Henry Schein</td>
			<td style="width:77px;">6540072</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">Sharp-pointed Dissecting Scissors (Straight; 4.5 inch)</td>
			<td style="width:147px;">Fisher Scientific</td>
			<td style="width:77px;">8940</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="34">
			<td height="34" style="height:34px;width:347px;">Buphrenorphine hydrochloride</td>
			<td style="width:147px;">Sigma-Aldrich</td>
			<td style="width:77px;">B9275</td>
			<td style="width:317px;">Use 0.03 mg/kg for both intra- and post-operatively for pain control</td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">Ampicillin, injectable</td>
			<td style="width:147px;">Henry Schein</td>
			<td style="width:77px;">1185678</td>
			<td style="width:317px;">Use 25 mg/kg subcutaneously during the procedure</td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">K-wire, 1.6 mm</td>
			<td style="width:147px;">Spectrum Surgical</td>
			<td style="width:77px;">SI040062</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;width:347px;">Keith Needle, Straight 1 1/2&#34;</td>
			<td style="width:147px;">Delasco Dermatology Lab &#38; Supply</td>
			<td style="width:77px;">KE-112</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="17">
			<td height="17" style="height:17px;width:347px;">Immunocal Decalcifying Solution</td>
			<td style="width:147px;">Fisher Scientific</td>
			<td>NC9491030</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="34">
			<td height="34" style="height:34px;width:347px;">Opticryl Acrylic Resin Bone Cement (PMMA) (Monomer and polymer)</td>
			<td style="width:147px;">US Dental Depot</td>
			<td style="width:77px;">OPTICRYL 100410&#160;</td>
			<td style="width:317px;"></td>
		</tr>
		<tr height="23">
			<td height="23" style="height:23px;width:347px;">Instron Model 5564 Tensile Testing Machine</td>
			<td style="width:147px;">Instron</td>
			<td style="width:77px;">5564</td>
			<td style="width:317px;">Any comparable tensile testing apparatus is suitable</td>
		</tr>
	</tbody>
</table>

athymic rat model for evaluation of engineered anterior cruciate ligament grafts

Anterior cruciate ligament (ACL) rupture is a common ligamentous injury that often requires surgery because the ACL does not heal well without intervention. Current treatment strategies include ligament reconstruction with either autograft or allograft, which each have their associated limitations. Thus, there is interest in designing a tissue-engineered graft for use in ACL reconstruction. We describe the fabrication of an electrospun polymer graft for use in ACL tissue engineering. This polycaprolactone graft is biocompatible, biodegradable, porous, and is comprised of aligned fibers. Because an animal model is necessary to evaluate such a graft, this paper describes an intra-articular athymic rat model of ACL reconstruction that can be used to evaluate engineered grafts, including those seeded with xenogeneic cells. Representative histology and biomechanical testing results at 16 weeks postoperatively are presented, with grafts tested immediately post-implantation and contralateral native ACLs serving as controls. The present study provides a reproducible animal model with which to evaluate tissue engineered ACL grafts, and demonstrates the potential of a regenerative medicine approach to treatment of ACL rupture.

En nuestra experiencia de 92 cirugías de rata por un solo cirujano, el tiempo medio operatorio desde la incisión hasta la finalización de la herida fue de 16,9 min, con una desviación estándar de 4,7 min. En el momento del sacrificio, ratas pesaban 356 ± 23 g. Todas las ratas toleraron la cirugía bien, y no experimentaron complicaciones. Inmediatamente después de la cirugía, se observaron las ratas para soportar el peso sobre la extremidad operativa, pero mostraron una leve cojera. Una semana después de la ope...

Watch this Scientific Journal Video about Athymic Rat Model for Evaluation of Engineered Anterior Cruciate Ligament Grafts at JoVE.com

Athymic Rat Model for Evaluation of Engineered Anterior Cruciate Ligament Grafts

Animal models are important tools for the evaluation of tissue-engineered grafts. This paper presents the protocol for preparing an electrospun biodegradable polymer graft for use in anterior cruciate ligament tissue engineering, as well as a surgical protocol for implantation in a rat model.

Atímicos Rata Modelo de Evaluación de Ingeniería de ligamento cruzado anterior injertos

Anterior cruciate ligament (ACL) rupture is a common ligamentous injury that often requires surgery because the ACL does not heal well without ...

athymic-rat-model-for-evaluation-engineered-anterior-cruciate

Research

JoVE Journal

Bioengineering

10.3K vistas.  University of California Los Angeles. Animal models are important tools for the evaluation of tissue-engineered grafts. This paper presents the protocol for preparing an electrospun biodegradable polymer graft for use in anterior cruciate ligament tissue engineering, as well as a surgical protocol for implantation in a rat model.

Video: Athymic Rat Model for Evaluation of Engineered Anterior Cruciate Ligament Grafts

Magnetic Resonance Elastography Methodology for the Evaluation of Tissue Engineered Construct Growth

Traditional mechanical testing often results in the destruction of the sample, and in the case of long term tissue engineered construct studies, the use of destructive assessment is not acceptable. A proposed alternative is the use of an imaging process called magnetic resonance elastography. Elastography is a nondestructive method for determining the engineered outcome by measuring local mechanical property values (i.e., complex shear modulus), which are essential markers for identifying the structure and functionality of a tissue. As a noninvasive means for evaluation, the monitoring of engineered constructs with imaging modalities such as magnetic resonance imaging (MRI) has seen increasing interest in the past decade1. For example, the magnetic resonance (MR) techniques of diffusion and relaxometry have been able to characterize the changes in chemical and physical properties during engineered tissue development2. The method proposed in the following protocol uses microscopic magnetic resonance elastography (&mu;MRE) as a noninvasive MR based technique for measuring the mechanical properties of small soft tissues3. MRE is achieved by coupling a sonic mechanical actuator with the tissue of interest and recording the shear wave propagation with an MR scanner4. Recently, &mu;MRE has been applied in tissue engineering to acquire essential growth information that is traditionally measured using destructive mechanical macroscopic techniques5. In the following procedure, elastography is achieved through the imaging of engineered constructs with a modified Hahn spin-echo sequence coupled with a mechanical actuator. As shown in Figure 1, the modified sequence synchronizes image acquisition with the transmission of external shear waves; subsequently, the motion is sensitized through the use of oscillating bipolar pairs. Following collection of images with positive and negative motion sensitization, complex division of the data produce a shear wave image. Then, the image is assessed using an inversion algorithm to generate a shear stiffness map6. The resulting measurements at each voxel have been shown to strongly correlate (R2&gt;0.9914) with data collected using dynamic mechanical analysis7. In this study, elastography is integrated into the tissue development process for monitoring human mesenchymal stem cell (hMSC) differentiation into adipogenic and osteogenic constructs as shown in Figure 2.

The procedure demonstrates the methodology of magnetic resonance elastography for monitoring the engineered outcome of adipose and osteogenic tissue engineered constructs through noninvasive local assessment of the mechanical properties using microscopic magnetic resonance elastography (&mu;MRE).

Metodología elastografía por resonancia magnética para la Evaluación de los tejidos Diseñado crecimiento Construct

Traditional mechanical testing often results in the destruction of the sample, and in the case of long term tissue engineered construct studies, the use ...

Investigación

Bioingeniería

Surgical Retrieval, Isolation and In vitro Expansion of Human Anterior Cruciate Ligament-derived Cells for Tissue Engineering Applications

Injury to the ACL is a commonly encountered problem in active individuals. Even partial tears of this intra-articular knee ligament lead to biomechanical deficiencies that impair function and stability. Current options for the treatment of partial ACL tears range from nonoperative, conservative management to multiple surgical options, such as: thermal modification, single-bundle repair, complete reconstruction, and reconstruction of the damaged portion of the native ligament. Few studies, if any, have demonstrated any single method for management to be consistently superior, and in many cases patients continue to demonstrate persistent instability and other comorbidities.
The goal of this study is to identify a potential cell source for utilization in the development of a tissue engineered patch that could be implemented in the repair of a partially torn ACL. A novel protocol was developed for the expansion of cells derived from patients undergoing ACL reconstruction. To isolate the cells, minced hACL tissue obtained during ACL reconstruction was digested in a Collagenase solution. Expansion was performed using DMEM/F12 medium supplemented with 10% fetal bovine serum (FBS) and 1% penicillin/streptomycin (P/S). The cells were then stored at -80 &#186;C or in liquid nitrogen in a freezing medium consisting of DMSO, FBS and the expansion medium. After thawing, the hACL derived cells were then seeded onto a tissue engineered scaffold, PLAGA (Poly lactic-co-glycolic acid) and control Tissue culture polystyrene (TCPS). After 7 days, SEM was performed to compare cellular adhesion to the PLAGA versus the control TCPS. Cellular morphology was evaluated using immunofluorescence staining. SEM (Scanning Electron Microscope) micrographs demonstrated that cells grew and adhered on both PLAGA and TCPS surfaces and were confluent over the entire surfaces by day 7. Immunofluorescence staining showed normal, non-stressed morphological patterns on both surfaces. This technique is promising for applications in ACL regeneration and reconstruction.

Surgical Retrieval, Isolation and In vitro Expansion of Human Anterior Cruciate Ligament-derived Cells for Tissue Engineering Applications

For future applications as a patch to repair partial tears of the Anterior Cruciate Ligament (ACL), human ACL derived cells were isolated from tissue obtained during reconstructive procedures, expanded in vitro and grown on tissue engineered scaffolds. Cellular adhesion and morphology was then performed to confirm biocompatibility on scaffold surface.

Recuperación Quirúrgica, aislamiento y<em&gt; In vitro</em&gt; Ampliación del cruzado anterior humana derivados de las células del ligamento para aplicaciones de ingeniería de tejidos

Injury to the ACL is a commonly encountered problem in active individuals. Even partial tears of this intra-articular knee ligament lead to biomechanical ...

Surgical Technique for the Implantation of Tissue Engineered Vascular Grafts and Subsequent In Vivo Monitoring

The development of Tissue Engineered Vessels (TEVs) is advanced by the ability to routinely and effectively implant TEVs (4-5 mm in diameter) into a large animal model. A step by-step protocol for inter-positional placement of the TEV and real-time digital assessment of the TEV and native carotid arteries is described here. In vivo monitoring is made possible by the implantation of flow probes, catheters and ultrasonic crystals (capable of recording dynamic diameter changes of implanted TEVs and native carotid arteries) at the time of surgery. Once implanted, researchers can calculate arterial blood flow patterns, invasive blood pressure and artery diameter yielding parameters such as pulse wave velocity, augmentation index, pulse pressures and compliance. Data acquisition is accomplished using a single computer program for analysis throughout the duration of the experiment. Such invaluable data provides insight into TEV matrix remodeling, its resemblance to native/sham controls and overall TEV performance in vivo.

Surgical Technique for the Implantation of Tissue Engineered Vascular Grafts and Subsequent In Vivo Monitoring

A step-by-step protocol for the inter-positional placement of Tissue Engineered Vessels (TEVs) into the carotid artery of a sheep using end-to-end anastomosis and real-time digital assessment in vivo until animal sacrifice.

Técnica quirúrgica para la implantación de la ingeniería tisular injertos vasculares y posterior<em&gt; En Vivo</em&gt; Monitoreo

The development of Tissue Engineered Vessels (TEVs) is advanced by the ability to routinely and effectively implant TEVs (4-5 mm in diameter) into a large ...

Production, Characterization and Potential Uses of a 3D Tissue-engineered Human Esophageal Mucosal Model

The incidence of both esophageal adenocarcinoma and its precursor, Barrett&#8217;s Metaplasia, are rising rapidly in the western world. Furthermore esophageal adenocarcinoma generally has a poor prognosis, with little improvement in survival rates in recent years. These are difficult conditions to study and there has been a lack of suitable experimental platforms to investigate disorders of the esophageal mucosa.
A model of the human esophageal mucosa has been developed in the MacNeil laboratory which, unlike conventional 2D cell culture systems, recapitulates the cell-cell and cell-matrix interactions present in vivo and produces a mature, stratified epithelium similar to that of the normal human esophagus. Briefly, the model utilizes non-transformed normal primary human esophageal fibroblasts and epithelial cells grown within a porcine-derived acellular esophageal scaffold. Immunohistochemical characterization of this model by CK4, CK14, Ki67 and involucrin staining demonstrates appropriate recapitulation of the histology of the normal human esophageal mucosa.
This model provides a robust, biologically relevant experimental model of the human esophageal mucosa. It can easily be manipulated to investigate a number of research questions including the effectiveness of pharmacological agents and the impact of exposure to environmental factors such as alcohol, toxins, high temperature or gastro-esophageal refluxate components. The model also facilitates extended culture periods not achievable with conventional 2D cell culture, enabling, inter alia, the study of the impact of repeated exposure of a mature epithelium to the agent of interest for up to 20 days. Furthermore, a variety of cell lines, such as those derived from esophageal tumors or Barrett&#8217;s Metaplasia, can be incorporated into the model to investigate processes such as tumor invasion and drug responsiveness in a more biologically relevant environment.

This manuscript describes the production, characterization and potential uses of a tissue engineered 3D esophageal construct prepared from normal primary human esophageal fibroblast and squamous epithelial cells seeded within a de-cellularized porcine scaffold. The results demonstrate the formation of a mature stratified epithelium similar to the normal human esophagus.

Producción, Caracterización y posibles usos de un Humano esofágica mucosas Modelo ingeniería tisular 3D

The incidence of both esophageal adenocarcinoma and its precursor, Barrett&#8217;s Metaplasia, are rising rapidly in the western world. Furthermore ...

Engineered 3D Silk-collagen-based Model of Polarized Neural Tissue

Despite huge efforts to decipher the anatomy, composition and function of the brain, it remains the least understood organ of the human body. To gain a deeper comprehension of the neural system scientists aim to simplistically reconstruct the tissue by assembling it in vitro from basic building blocks using a tissue engineering approach. Our group developed a tissue-engineered silk and collagen-based 3D brain-like model resembling the white and gray matter of the cortex. The model consists of silk porous sponge, which is pre-seeded with rat brain-derived neurons, immersed in soft collagen matrix. Polarized neuronal outgrowth and network formation is observed with separate axonal and cell body localization. This compartmental architecture allows for the unique development of niches mimicking native neural tissue, thus enabling research on neuronal network assembly, axonal guidance, cell-cell and cell-matrix interactions and electrical functions.

Insight into the complex actions of the brain requires advanced research tools. Here we demonstrate a novel silk-collagen-based 3D engineered model of neural tissue resembling brain-like architecture. The model can be used to study neuronal network assembly, axonal guidance, cell-cell interactions and electrical activity.

Modelo de polarizado Neural tisular basada Silk-colágeno-Engineered 3D

Despite huge efforts to decipher the anatomy, composition and function of the brain, it remains the least understood organ of the human body. To gain a ...

Applications of In Vivo Functional Testing of the Rat Tibialis Anterior for Evaluating Tissue Engineered Skeletal Muscle Repair

Despite the regenerative capacity of skeletal muscle, permanent functional and/or cosmetic deficits (e.g., volumetric muscle loss (VML) resulting from traumatic injury, disease and various congenital, genetic and acquired conditions are quite common. Tissue engineering and regenerative medicine technologies have enormous potential to provide a therapeutic solution. However, utilization of biologically relevant animal models in combination with longitudinal assessments of pertinent functional measures are critical to the development of improved regenerative therapeutics for treatment of VML-like injuries. In that regard, a commercial muscle lever system can be used to measure length, tension, force and velocity parameters in skeletal muscle. We used this system, in conjunction with a high power, bi-phase stimulator, to measure in vivo force production in response to activation of the anterior crural compartment of the rat hindlimb. We have previously used this equipment to assess the functional impact of VML injury on the tibialis anterior (TA) muscle, as well as the extent of functional recovery following treatment of the injured TA muscle with our tissue engineered muscle repair (TEMR) technology. For such studies, the left foot of an anaesthetized rat is securely anchored to a footplate linked to a servomotor, and the common peroneal nerve is stimulated by two percutaneous needle electrodes to elicit muscle contraction and dorsiflexion of the foot. The peroneal nerve stimulation-induced muscle contraction is measured over a range of stimulation frequencies (1-200 Hz), to ensure an eventual plateau in force production that allows for an accurate determination of peak tetanic force. In addition to evaluation of the extent of VML injury as well as the degree of functional recovery following treatment, this methodology can be easily applied to study diverse aspects of muscle physiology and pathophysiology. Such an approach should assist with the more rational development of improved therapeutics for muscle repair and regeneration.

Applications of In Vivo Functional Testing of the Rat Tibialis Anterior for Evaluating Tissue Engineered Skeletal Muscle Repair

We describe an in vivo protocol to measure dorsiflexion of the foot following stimulation of the peroneal nerve and contraction of the anterior crural compartment of the rat hindlimb. Such measurements are an indispensable translational tool for evaluating skeletal muscle pathology and tissue engineering approaches to muscle repair and regeneration.

Aplicaciones de la<em&gt; En Vivo</em&gt; Pruebas funcionales de la rata tibial anterior para la evaluación de la ingeniería tisular de reparación del músculo esquelético

Despite the regenerative capacity of skeletal muscle, permanent functional and/or cosmetic deficits (e.g., volumetric muscle loss (VML) resulting from ...

Scaling of Engineered Vascular Grafts Using 3D Printed Guides and the Ring Stacking Method

Coronary artery disease remains a leading cause of death, affecting millions of Americans. With the lack of autologous vascular grafts available, engineered grafts offer great potential for patient treatment. However, engineered vascular grafts are generally not easily scalable, requiring manufacture of custom molds or polymer tubes in order to customize to different sizes, constituting a time-consuming and costly practice. Human arteries range in lumen diameter from about 2.0-38 mm and in wall thickness from about 0.5-2.5 mm. We have created a method, termed the "Ring Stacking Method," in which variable size rings of tissue of the desired cell type, demonstrated here with vascular smooth muscle cells (SMCs), can be created using guides of center posts to control lumen diameter and outer shells to dictate vessel wall thickness. These tissue rings are then stacked to create a tubular construct, mimicking the natural form of a blood vessel. The vessel length can be tailored by simply stacking the number of rings required to constitute the length needed. With our technique, tissues of tubular forms, similar to a blood vessel, can be readily manufactured in a variety of dimensions and lengths to meet the needs of the clinic and patient.

Scalable engineered blood vessels would improve clinical applicability. Using easily sizable 3D-printed guides, rings of vascular smooth muscle were created and stacked into a tubular form, forming a vascular graft. Grafts can be sized to meet the range of human coronary artery dimensions by simply changing the 3D-printed guide size.

El escalado de Engineered injertos vasculares Usando 3D Impreso guías y el método de anillo de apilamiento

Coronary artery disease remains a leading cause of death, affecting millions of Americans. With the lack of autologous vascular grafts available, ...

Treatment of Ligament Constructs with Exercise-conditioned Serum: A Translational Tissue Engineering Model

In vitro experiments are essential to understand biological mechanisms; however, the gap between monolayer tissue culture and human physiology is large, and translation of findings is often poor. Thus, there is ample opportunity for alternative experimental approaches. Here we present an approach in which human cells are isolated from human anterior cruciate ligament tissue remnants, expanded in culture, and used to form engineered ligaments. Exercise alters the biochemical milieu in the blood such that the function of many tissues, organs and bodily processes are improved. In this experiment, ligament construct culture media was supplemented with experimental human serum that has been &#39;conditioned&#39; by exercise. Thus the intervention is more biologically relevant since an experimental tissue is exposed to the full endogenous biochemical milieu, including binding proteins and adjunct compounds that may be altered in tandem with the activity of an unknown agent of interest. After treatment, engineered ligaments can be analyzed for mechanical function, collagen content, morphology, and cellular biochemistry. Overall, there are four major advantages versus traditional monolayer culture and animal models, of the physiological model of ligament tissue that is presented here. First, ligament constructs are three-dimensional, allowing for mechanical properties (i.e., function) such as ultimate tensile stress, maximal tensile load, and modulus, to be quantified. Second, the enthesis, the interface between boney and sinew elements, can be examined in detail and within functional context. Third, preparing media with post-exercise serum allows for the effects of the exercise-induced biochemical milieu, which is responsible for the wide range of health benefits of exercise, to be investigated in an unbiased manner. Finally, this experimental model advances scientific research in a humane and ethical manner by replacing the use of animals, a core mandate of the National Institutes of Health, the Center for Disease Control, and the Food and Drug Administration.

We present a model of ligament tissue in which three-dimensional constructs are treated with the human exercise-conditioned serum and analyzed for collagen content, function, and cellular biochemistry.

Tratamiento de las estructuras de ligamentos con suero acondicionado con ejercicio: Un modelo de ingeniería de tejidos traslacional

In vitro experiments are essential to understand biological mechanisms; however, the gap between monolayer tissue culture and human physiology is large, ...

Use of High-Throughput Automated Microbioreactor System for Production of Model IgG1 in CHO Cells

Automated microscale bioreactors (15 mL) can be a useful tool for cell culture engineers. They facilitate the simultaneous execution of a wide variety of experimental conditions while minimizing potential process variability. Applications of this approach include: clone screening, temperature and pH shifts,&#160;media and supplement optimization. Furthermore, the small reactor volumes are conducive to large Design of Experiments that investigate a wide range of conditions. This allows upstream processes to be significantly optimized before scale-up where experimentation is more limited in scope due to time and economic constraints. Automated microscale bioreactor systems offer various advantages over traditional small scale cell culture units, such as shake flasks or spinner flasks. However, during pilot scale process development&#160;significant care must be taken to ensure that these advantages are realized. When run with care, the system can enable high level automation, can be programmed to run DOE&#39;s with a higher number of variables&#160;and can reduce sampling time when integrated with a nutrient analyzer or cell counter. Integration of the expert-derived heuristics presented here, with current automated microscale bioreactor experiments can minimize common pitfalls that hinder meaningful results. In the extreme, failure to adhere to the principles laid out here can lead to equipment damage that requires expensive repairs. Furthermore, the microbioreactor systems have small culture volumes&#160;making characterization of cell culture conditions difficult. The number and amount of samples taken in-process in batch mode culture is limited as operating volumes cannot fall below 10 mL. This method will discuss the benefits and drawbacks of microscale bioreactor systems.

A detailed protocol for the concurrent operation of 48 parallel cell cultures under varied conditions in a microbioreactor system is presented. Cell culture process, harvest and subsequent antibody titer analysis are described.

Microbioreactor uso de alto rendimiento automático para la producción de IgG1 modelo en células CHO

Automated microscale bioreactors (15 mL) can be a useful tool for cell culture engineers. They facilitate the simultaneous execution of a wide variety of ...

Rat Model of Adhesive Capsulitis of the Shoulder

This proposal aims to create an in vivo rat model of adhesive capsulitis for researching potential treatment options for this condition and other etiologies of comparable arthrofibrosis. The model includes extra-articular fixation of the shoulder in rats via scapular to humeral suturing, resulting in a secondary contracture without invading the intra-articular space and resulting in decreased rotational ROM and increased joint stiffness.
We used 10 Sprague-Dawley rats for the purpose of this study. Baseline ROM measurements were taken before glenohumeral immobilization. The rats were subjected to 8 weeks of immobilization before the fixation sutures were removed and changes in ROM and joint stiffness were evaluated. To evaluate whether immobilization resulted in a significant reduction in ROM, changes in kinematics were calculated. ROM was measured at each time point in the follow-up period and was compared to the baseline internal and external ROM measurements. In order to evaluate the stiffness, joint kinetics were calculated by determining the differences in torque (text and tint ) needed to reach the initial external rotation of 60&#176; and initial internal rotation of 80&#176;.
After the removal of the extra-articular suture fixation on follow-up day 0, we found a 63% decrease in total ROM compared to baseline. We observed continuous improvement until week 5 of follow-up, with the progress slowing down around a 19% restriction. On week 8 of follow-up, there was still an 18% restriction of ROM. Additionally, on follow-up day 0, we found the torque increased by 13.3 Nmm when compared to baseline. On week 8, the total torque was measured to be 1.4 &#177; 0.2 Nmm higher than initial measurements. This work introduces a rat model of shoulder adhesive capsulitis with lasting reduced ROM and increased stiffness.

This protocol presents an in vivo rat model of adhesive capsulitis. The model includes an internal fixation of the glenohumeral joint with extra-articular suture fixation for an extended time, resulting in a decreased rotational range of motion (ROM) and increased joint stiffness.