Name: 3d hydrogel scaffolds for articular chondrocyte culture and cartilage generation
Uploaded: 2015-10-07T14:00:00.000+00:00
Duration: 12 min 37 s
Description: Watch this Scientific Journal Video about 3D Hydrogel Scaffolds for Articular Chondrocyte Culture and Cartilage Generation at JoVE.com

The authors would like to acknowledge Stanford Department of Orthopaedic Surgery and Stanford Coulter Translational Seed Grant for funding. J.H.L. would like to thank National Science Foundation Graduate Fellowship and DARE Doctoral Fellowship for support.

Tutti gli esperimenti sono stati eseguiti in conformità con le linee guida dei soggetti Stanford University Umani e approvati protocollo Institutional Review Board. Isolamento 1. articolare di condrociti <ol><li> Ottenere la cartilagine da tessuti scartati durante protesi totale di ginocchio e sezionare come descritto in precedenza 8. </li><li> Visivamente selezionare i condili femorali mediale o laterale di campioni di cartilagine per superfici lisce e rendere incisione alla superficie della cartilagine attraverso un bisturi per rimuovere 4-5 biopsie mm cartilagine senza influenzare l&#39;osso subcondrale. </li><li> Isolare condrociti dalla matrice extracellulare per dissociazione enzimatica del tessuto con il trattamento / N O con collagenasi purificata. Utilizzare rapporto 1: 1 di collagenasi II (125 U / ml) e Collagenasi IV (160 U / ml) in terreni di coltura di condrociti a 37 ° C. </li><li> Il giorno seguente, filtrare il tessuto digerito contenente le cellule dissociate attraverso un 70mm pori maglie di dimensione nylon. Lavare due volte con 20 ml di DMEM / F12 e centrifugare a 600 xg per 5 min. </li><li> Piastra le condrociti isolati ad una densità di 1 x 10 6 cellule / 60 mm piatto di coltura dopo risospensione in DMEM / F12 addizionato con 10% Fetal Bovine Serum (FBS), 25 mg / ascorbato ml, 2 mM L-glutammina, antimicrobici (100 U / ml di penicillina, 100 mg / ml di streptomicina, e 0,25 mg / ml Fungizone). Conservare le piastre a 37 ° C e mantenere le colture di condrociti primari come un monostrato alta densità prima incapsulamento in idrogel biomimetici. </li></ol> 2. Biomimetic Hydrogel Fabrication NOTA: Questo metodo permette la sintesi di un idrogel biomimetico contenente poli (etilene glicol diacrilato) (PEGDA, MW 5000 g / mole), condroitin solfato-metacrilato (CS-MA) in DPBS. L&#39;aggiunta di fotoiniziatore permette reticolazione fotoattivato. La composizione idrogel finale contiene il 7% pesaret / Volume (w / v) di PEGDA, 3% w / v di CS-MA, e 0,05% w / v di fotoiniziatore. <ol><li> Sintetizzare CS-MA per funzionalizzazione CS polimero con gruppi di metacrilato. <ol><li> Preparare la soluzione tampone di 50 mM di acido 2-morpholinoethanesulfonic (MES) e 0,5 M di cloruro di sodio (NaCl) sciogliendo 1,952 g di MES e 5,84 g di NaCl in 200 ml di acqua deionizzata (DIH 2 O). Sciogliere 5 g di sale di condroitin solfato sodico nella soluzione tamponata. </li><li> Aggiungere 0,532 g (4,62 mmol) N-idrossisuccinimmide (NHS) e 1.771 g (9.24 mmol) 1-etil-3- (3-dimetilamminopropil) cloridrato -carbodiimide (EDC) (rapporto molare di NHS: EDC = 1: 2) a la soluzione e mescolare per 5 min. </li><li> Aggiungere 0,765 g (4,62 mmol) metacrilato di 2-amminoetil (Aema) (rapporto molare di NHS: EDC: Aema = 1: 2: 1) alla soluzione e mantenere la reazione a temperatura ambiente per 24 ore. </li><li> Purificare il composto con la dialisi contro acqua deionizzata (diH 2 O) per 4 giorni usando tubo di dialisi (12-14 kDa MWCO). </li><li> Filtrare la purified soluzione attraverso un filtro di 0,22 micron e posizionare i tubi aperti contenenti la soluzione in un essiccatore sotto vuoto e O / N. Assicurarsi che tutti i tubi siano protetti dalla luce. Conservare il polimero sciolto a -20 ° C al riparo dalla luce e dall&#39;umidità. </li></ol></li></ol> Incapsulamento 3. cellulare <ol><li> Autoclave i film e cilindrici aste PCR (per punzonatura gli idrogel 3D cell-carico) e sterilizzare lo stampo gel cilindrica su misura per immersione in 0,2 micron filtrato etanolo al 70% in cappuccio coltura tissutale sotto raggi UV. </li><li> Sigillare il fondo dello stampo gel con pellicola PCR autoclave senza bolle d&#39;aria o lacune per impedire perdite. Tenerlo in una piastra sterile, 150 millimetri. </li><li> Il giorno prima di incapsulamento delle cellule in idrogel biomimetica, dissociare il condrociti monostrato ad alta densità con trattamento O / N in Collagenase II e soluzione Collagenasi IV. Utilizzare 125 U / ml per Collagenasi II e 160 U / ml per Collagenasi VI ciascuno in crescita di condrociti dei mediaa 37 ° C. </li><li> Dai tubo da 50 ml e si aggiungono 5% peso / volume (w / v) di poli (etilene glicol diacrilato) (PEGDA, MW = 5,000 g / mole), 3% w / v condroitin solfato-metacrilato (CS-MA), e 0.05% w / v fotoiniziatore in DPBS. Agitare la provetta per miscelare la soluzione e tenerlo da parte. Proteggere il tubo dalla luce. </li><li> Raccogliere le cellule dissociate in un tubo Falcon da 50 ml, contare e centrifugare a 460 xg per 5 min. Aspirare tutti i media dal tubo cellule e aggiungere il materiale sopra il gel miscelato risospendere le cellule ad una densità di 15 × 10 6 cellule / ml. Mescolare 30 volte a fondo, evitando la formazione di bolle d&#39;aria. </li><li> Dispensare 72 ml di sospensione cellulare-idrogel o da soli idrogel nello stampo gel cilindrica su misura e indurre gelificazione attraverso l&#39;esposizione alla luce UV (365 nm) a 3 mW / m 2 per 5 min. Preparare una soluzione idrogel senza contenuto della cella. Utilizzare questi costrutti come controlli negativi per il futuro i test biochimici e meccanici. Misure l&#39;intensità della luce UV con un misuratore di intensità UV. Per regolare l&#39;intensità, modificare la distanza tra la sorgente di luce UV e il ponteggio idrogel durante la gelificazione. NOTA: Dal momento che l&#39;idrogel contiene CS, il contributo acellulare viene sottratto dal contenuto GAG biochimica degli idrogel cellulari carichi di rappresentare solo il GAG cellulare. </li><li> Utilizzare un bisturi per tagliare il film per easy peel e rimuovere con cautela. Con l&#39;aiuto delle aste cilindriche, spingere fuori il gel in una piastra ben 6 con 5 ml di DPBS sterili per lavare gel polimerizzato e cellule allentati. </li><li> Culture idrogel cellulari carichi in piastre da 24 pozzetti contenenti 1,5 ml di terreni di crescita di condrociti in ogni pozzetto. Utilizzare una spatola monouso per trasferire i idrogel lavati nel pozzo. </li><li> Valutare la vitalità cellulare del morto in diretta colorazione 24 ore post-incapsulamento utilizzando un kit di sopravvivenza / citotossicità. Cultura idrogel cellulari carichi e gli idrogeli vuote per 3-6 settimane che cambiano a gro chondrocyte freschiwth dei media ogni 2 giorni prima della raccolta per le analisi. </li></ol> 4. RNA Estrazione e Gene Expression analisi <ol><li> Aspirare accuratamente la memoria e poi PBS sterile 1X sulla cellula-carico nonché gli idrogeli controllo vuote. </li><li> Con l&#39;aiuto di una spatola sterile, trasferire ogni idrogel di clean 1,5 ml provetta Eppendorf e aggiungere 250 ml di Tri-reattivo ad ogni provetta. Seguire le istruzioni del produttore per isolare l&#39;RNA. </li><li> Dopo l&#39;isolamento di RNA e quantificazione uso 1 mg di esso da ogni campione e di eseguire una trascrizione inversa in cDNA utilizzando l&#39;alta capacità cDNA corredo d&#39;inversione di trascrizione. </li><li> Per PCR quantitativa utilizzare TaqMan array di espressione genica per l&#39;esame dell&#39;espressione di geni di interesse. Normalizzare i livelli di espressione genica internamente per GAPDH. </li><li> Per le condizioni di PCR includere un 2 min di incubazione a 50 ° C per inattivare ampliconi precedenti con glicosilasi uracile-DNA, seguito da 1060; min di incubazione a 95 ° C per attivare la polimerasi Taq. Quindi eseguire cicli di PCR quaranta, costituito da 15 sec a 95 ° C, e 1 minuto a 60 ° C. </li></ol> 5. Analisi biochimiche <ol><li> Per ogni costruzioni cellulari-idrogel quantificare il DNA e glicosaminoglicani solfato (sGAG) la produzione come segue. </li><li> Aspirare accuratamente la memoria e poi PBS sterile 1X sulla cellula-carico nonché gli idrogeli controllo vuote. Pesare un tubo vuoto e mettere l&#39;idrogel all&#39;interno dopo assorbente su carta velina e registrare il peso o il peso umido degli idrogel. </li><li> Congelare ogni idrogel a -20 ° C in un tubo separato ml eppendorf 1.5 per digestione enzimatica e successivamente utilizzare una aliquota di prodotto digerita eseguire PicoGreen dosaggio (DNA) e dimetil-metilene assay blu (GAG). </li><li> Preparare la soluzione papainase per digestione enzimatica degli idrogel. <ol><li> Per prima cosa preparate il buffer PBE pesando 7,1 g di sodio phosphate bibasico (Na 2 HPO 4) e 1,6 g di acido etilendiamminotetracetico disodico sale (EDTA-Na 2). Sciogliere in 500 ml di dH 2 O, regolare il pH a 6,5 e filtrare la soluzione purificata attraverso un filtro 0.22 mm. </li><li> Sciogliere 0,035 g di L-cisteina in 20 ml di tampone PBE. Filtrare la soluzione e 100 ml di sterile papaina enzima. </li></ol></li><li> Al momento di eseguire saggi, prendere le provette da -20 ° C e aggiungere 300 microlitri della soluzione papaina pronto a idrogel congelati. Schiacciare il gel con un mortaio e pestello e mescolare bene con il pestello motore. </li><li> Portare il volume a 500 ml con soluzione papaina aggiuntivo. Eseguire la stessa procedura per i gel di controllo. Incubare a 60 ° C per 16 ore 3,9. La soluzione contenente l&#39;idrogel digerito può quindi utilizzato per il DNA e GAG ​​quantificazione. Misurare il contenuto di DNA con il saggio PicoGreen con Lambda fago DNA di serie seguente pr del produttoreotocol. </li><li> Quantificare il contenuto solfato-GAG utilizzando il blu 1,9-metilmetilene (DMMB)-dye legame test con squalo condroitin solfato di serie 10. Determinare il contenuto di GAG dividendo l&#39;importo di GAG per la corrispondente peso umido. </li></ol> 6. Prove meccaniche <ol><li> Eseguire prove di compressione non confinati usando un sistema di prova Instron 5944 dotato di una cella di carico di 10 N. <ol><li> Dopo i giorni desiderati di coltura in vitro, eseguire il test di compressione sull&#39;impalcatura cellula-idrogel e gli idrogeli controllo acellulari. </li><li> Immergere i campioni in un bagno PBS a temperatura ambiente e comprimere ad un tasso del 1% ceppo / sec per un ceppo massimo del 15% 11,12 dal momento che la sforzo fisico vissuta da tessuto cartilagineo sotto condizioni di carico è stato segnalato per essere 10-20% 13,14. </li></ol></li><li> Creare lo stress contro curve deformazione e la curva in forma con un terzo ordine un&#39;equazione polinomiale. Determinare i compressive tangente modulo dalla curva equazione forma in valori di deformazione del 15%. </li></ol>

<ol>
	<li>Roberts, S., Menage, J., Sandell, L. J., Evans, E. H., Richardson, J. B. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Immunohistochemical+study+of+collagen+types+I+and+II+and+procollagen+IIA+in+human+cartilage+repair+tissue+following+autologous+chondrocyte+implantation.">Immunohistochemical study of collagen types I and II and procollagen IIA in human cartilage repair tissue following autologous chondrocyte implantation.</a> Knee. 16, 398-404 (2009).</li><li>Smeriglio, P., 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=Comparative+Potential+of+Juvenile+and+Adult+Human+Articular+Chondrocytes+for+Cartilage+Tissue+Formation+in+Three-Dimensional+Biomimetic+Hydrogels.">Comparative Potential of Juvenile and Adult Human Articular Chondrocytes for Cartilage Tissue Formation in Three-Dimensional Biomimetic Hydrogels.</a> Tissue engineering. Part A. , (2014).</li><li>Lai, J. H., Kajiyama, G., Smith, R. L., Maloney, W., Yang, F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Stem+cells+catalyze+cartilage+formation+by+neonatal+articular+chondrocytes+in+3D+biomimetic+hydrogels.">Stem cells catalyze cartilage formation by neonatal articular chondrocytes in 3D biomimetic hydrogels.</a> Scientific reports. 3, 3553 (2013).</li><li>Taipale, J., Keski-Oja, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Growth+factors+in+the+extracellular+matrix.">Growth factors in the extracellular matrix.</a> FASEB journal : official publication of the Federation of American Societies for Experimental Biology. 11, 51-59 (1997).</li><li>Varghese, S., 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=Chondroitin+sulfate+based+niches+for+chondrogenic+differentiation+of+mesenchymal+stem+cells.">Chondroitin sulfate based niches for chondrogenic differentiation of mesenchymal stem cells.</a> Matrix Biol. 27, 12-21 (2008).</li><li>Park, J. S., 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+effect+of+matrix+stiffness+on+the+differentiation+of+mesenchymal+stem+cells+in+response+to+TGF-beta.">The effect of matrix stiffness on the differentiation of mesenchymal stem cells in response to TGF-beta.</a> Biomaterials. 32, 3921-3930 (2011).</li><li>Wang, T., Lai, J. H., Han, L. H., Tong, X., Yang, F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Chondrogenic+Differentiation+of+Adipose-Derived+Stromal+Cells+in+Combinatorial+Hydrogels+Containing+Cartilage+Matrix+Proteins+with+Decoupled+Mechanical+Stiffness.">Chondrogenic Differentiation of Adipose-Derived Stromal Cells in Combinatorial Hydrogels Containing Cartilage Matrix Proteins with Decoupled Mechanical Stiffness.</a> Tissue engineering. Part A. , (2014).</li><li>Smith, R. 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=Effects+of+intermittent+hydrostatic+pressure+and+BMP-2+on+osteoarthritic+human+chondrocyte+metabolism+in+vitro.">Effects of intermittent hydrostatic pressure and BMP-2 on osteoarthritic human chondrocyte metabolism in vitro.</a> J Orthop Res. 29, 361-368 (2011).</li><li>Buschmann, M. D., Gluzband, Y. A., Grodzinsky, A. J., Kimura, J. H., Hunziker, E. B. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Chondrocytes+in+agarose+culture+synthesize+a+mechanically+functional+extracellular+matrix.">Chondrocytes in agarose culture synthesize a mechanically functional extracellular matrix.</a> J Orthop Res. 10, 745-758 (1992).</li><li>Farndale, R. W., Buttle, D. J., Barrett, A. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Improved+quantitation+and+discrimination+of+sulphated+glycosaminoglycans+by+use+of+dimethylmethylene+blue.">Improved quantitation and discrimination of sulphated glycosaminoglycans by use of dimethylmethylene blue.</a> Biochim Biophys Acta. 883, 173-177 (1986).</li><li>Lai, J. H., Levenston, M. E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Meniscus+and+cartilage+exhibit+distinct+intra-tissue+strain+distributions+under+unconfined+compression.">Meniscus and cartilage exhibit distinct intra-tissue strain distributions under unconfined compression.</a> Osteoarthritis and cartilage / OARS, Osteoarthritis Research Society. 18, 1291-1299 (2010).</li><li>Li, L. P., Buschmann, M. D., Shirazi-Adl, A. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Strain-rate+dependent+stiffness+of+articular+cartilage+in+unconfined+compression.">Strain-rate dependent stiffness of articular cartilage in unconfined compression.</a> Journal of biomechanical engineering. 125, 161-168 (2003).</li><li>Armstrong, C. G., Bahrani, A. S., Gardner, D. L. <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+measurement+of+articular+cartilage+deformations+in+the+intact+human+hip+joint+under+load.">In vitro measurement of articular cartilage deformations in the intact human hip joint under load.</a> The Journal of bone and joint surgery. American. 61, 744-755 (1979).</li><li>Macirowski, T., Tepic, S., Mann, R. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Cartilage+stresses+in+the+human+hip+joint.">Cartilage stresses in the human hip joint.</a> Journal of biomechanical engineering. 116, 10-18 (1994).</li><li>Benya, P. D., Shaffer, J. D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Dedifferentiated+chondrocytes+reexpress+the+differentiated+collagen+phenotype+when+cultured+in+agarose+gels.">Dedifferentiated chondrocytes reexpress the differentiated collagen phenotype when cultured in agarose gels.</a> Cell. 30, 215-224 (1982).</li><li>Buckwalter, J. A., Mankin, H. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Articular+cartilage:+tissue+design+and+chondrocyte-matrix+interactions.">Articular cartilage: tissue design and chondrocyte-matrix interactions.</a> Instructional course lectures. 47, 477-486 (1998).</li><li>Wang, D. A., 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=Multifunctional+chondroitin+sulphate+for+cartilage+tissue-biomaterial+integration.">Multifunctional chondroitin sulphate for cartilage tissue-biomaterial integration.</a> Nat Mater. 6, 385-392 (2007).</li><li>Simson, J. A., Strehin, I. A., Allen, B. W., Elisseeff, 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=Bonding+and+fusion+of+meniscus+fibrocartilage+using+a+novel+chondroitin+sulfate+bone+marrow+tissue+adhesive.">Bonding and fusion of meniscus fibrocartilage using a novel chondroitin sulfate bone marrow tissue adhesive.</a> Tissue engineering. Part A. 19, 1843-1851 (2013).</li></ol>

The authors have nothing to disclose.

Come riportato in questo protocollo, gli idrogel 3D sono in grado di mantenere condrociti fenotipo nella cultura, evitando il processo di de-differenziazione delle cellule in cellule fibrocartilagine riscontrate in genere con colture monostrato 15. Inoltre, le colture a lungo termine di idrogel costrutto chondrocytes- rivelato un ambiente favorevole che mantiene le caratteristiche intrinseche delle cellule associate con l&#39;età e la malattia. L&#39;uso di un idrogel biomimetico 3D ha diversi vantaggi. In primo luogo, l&#39;inclusione di condroitin solfato (CS), uno dei principali componenti trovati nella cartilagine articolare, attivare le cellule di degradare la matrice idrogel secernendo condroitinasi e stabilire la cartilagine nuova sintesi extracellulare matrice 5, 16. Inoltre, CS è stato dimostrato per avere proprietà anti-infiammatorie nel giunto artritico. L&#39;idrogel biomimetico può anche essere usato come materiale per la consegna ponteggio cella riparazione della cartilagine, e può essere modificato chimicamenteper facilitare una migliore integrazione dei tessuti 17,18-biomateriale. L&#39;uso degli idrogel PEG-CS consente colture a lungo termine di condrociti e la valutazione delle proprietà biochimiche e meccaniche. Qui mostriamo come questa piattaforma può essere utile per le analisi comparative delle varie fonti di condrociti differenziati al fine di definire il tipo cellulare ottimale per l&#39;ingegneria cartilagine. È interessante notare che, condrociti incapsulate in idrogel rimangono vitali e proliferano in base alle loro capacità intrinseche. I supporti composizione idrogel, infatti, la crescita di giovani e adulti condrociti sani come mostrato in Figura 2. La composizione e la struttura degli idrogel descritti promuove anche la formazione di tessuto cartilagineo come indicato dalla deposizione di matrice extracellulare funzionale valutata glicosaminoglicani (GAG ) quantificazione. Un ulteriore vantaggio è che i costrutti chondrocyte-idrogelpuò essere valutata per le proprietà meccaniche del tessuto cartilagineo neoformato. Si noti che il test di compressione non confinato dovrebbe essere eseguita sul idrogel acellulare per il confronto. Gli idrogeli, infatti, hanno una rigidità intrinseca dovuta alla rigidità delle porzioni CS. Ceppo compressione unconfined del 5-20% (a velocità di deformazione 1% / s) può essere applicato per la prove meccaniche della cartilagine tessuto 11,12 in quanto il ceppo fisiologico sperimentato da tessuto cartilagineo sotto condizioni di carico è stato segnalato per essere 10-20 13,14%. La risposta delle cellule sia carichi e acellulari idrogel a prove meccaniche è stata valutata al punto finale cultura. Nell&#39;esempio descritto sopra osservato una rigidità paragonabile dei costrutti contenenti adulti e giovanili condrociti in contrasto con la rigidità inferiore dei costrutti contenenti condrociti OA. Tali proprietà meccaniche del costrutto cellule idrogel permettono la valutazione delle proprietà funzionali deltessuto formata dando una analisi approfondita della capacità maturazione delle cellule. In conclusione, l&#39;utilizzo degli idrogel biomimetici 3D per studiare il potenziale della popolazione condrociti diverso per generare tessuto cartilagineo può essere ampiamente applicato. Oltre agli studi in vitro qui descritti, trapianto in vivo dei costrutti cellulari carichi può essere prevista per studiare la maturazione delle cellule e potenziale rigenerativo nel contesto fisiologico. Ulteriori modifiche della piattaforma idrogel con ulteriori fattori biomimetici possono anche essere immaginato per ottimizzare la proliferazione di condrociti e maturazione.

With its limited self-repair potential, human articular cartilage undergoes frequent irreversible damages. Extensive efforts are currently focused on the development of efficient cell-based approaches for treatment of articular cartilage injuries. The success of these cell-based therapies is highly dependent on the selection of an optimal cell source and the maintenance of its regenerative potential. Chondrocytes are a common cell source for cartilage repair, but they are limited in supply and can de-differentiate during in vitro expansion in 2D monolayer culture thereby limiting their generation of hyaline cartilage 1. 
The aim of this protocol is to establish a 3-dimensional hydrogel platform for an in vitro comparative study of human chondrocytes from different ages and disease state. Unlike conventional two-dimensional (2D) culture, three-dimensional (3D) hydrogels allow chondrocytes to maintain their morphology and phenotype and provides a physiologically relevant environment enabling chondrocytes to produce cartilage tissue 2,3. In addition to providing a 3D physical structure for chondrocyte culture, hydrogels mimic the function of native cartilage extracellular matrix (ECM). Specifically, the inclusion of chondroitin sulfate methacrylate provides a potential reservoir for secreted paracrine factors 4 and enables cell-mediated degradation and matrix turnover 5. Although many 3D hydrogel culture systems have been utilized widely in various studies including agarose and alginate gels, we have used a biomimetic 3D culture system that has some distinct advantages for chondrocyte culture. Chondroitin sulfate (CS) is an abundant component in articular cartilage and the PEG-CS hydrogels have been shown to maintain and even enhance chondrogenic phenotype and facilitate cell-mediated matrix degradation and turnover 2,5. In addition, the mechanical properties of the hydrogel scaffold can be easily modulated by changing concentration of PEG and hence can be utilized to further enhance the regeneration potential of chondrocytes or a related cell type 6,7. PEG/CSMA is also biocompatible and hence has the potential for a direct clinical application in cartilage defects for example. The limitation for this system is its complexity and the use of photopolymerization that can potentially affect cell viability as compared to simpler systems like agarose, however the advantages for the chondrocyte culture outweigh the potential limitations.
The 3D hydrogel culture is compatible with conventional assay for evaluation of cell phenotype (gene expression, protein immunostaining) and functional outcome (quantification of cartilage matrix production, mechanical testing). This favorable 3D environment was tested to compare the tissue regeneration potential of human chondrocytes from three different aged populations in long-term 3D cultures. 
The outcomes were evaluated via both phenotypic and functional assays. Juvenile, adult and OA chondrocytes showed differential responses in the 3D biomimetic hydrogel culture. After 3 and 6 weeks, chondrogenic gene expression was upregulated in juvenile and adult chondrocytes but was downregulated in OA chondrocytes. Deposition of cartilage tissue components including aggrecan, type II collagen, and glycosaminoglycan (GAG) was high for juvenile and adult chondrocytes but not for OA chondrocytes. The compressive moduli of the resulting cartilage constructs also exhibited similar trends. In conclusion, both juvenile and adult chondrocytes exhibited chondrogenic and cartilage matrix disposition up to 6 weeks of 3D culture in hydrogels. In contrast, osteoarthritic chondrocytes revealed a loss of cartilage phenotype and minimal ability to generate robust cartilage.

<table><tbody><tr><td>juvenile chondrocytes (Clonetics Normal Human Chondrocyte Cell System )</td><td>Lonza</td><td>CC-2550</td><td></td></tr><tr><td>adult chondrocytes (Clonetics Normal Human Chondrocyte Cell System)</td><td>Lonza</td><td>CC-2550</td><td></td></tr><tr><td>poly(ethylene glycol diacrylate)</td><td>Laysan Bio</td><td>ACRL-PEG-ACRL-1000-1g</td><td></td></tr><tr><td>2-morpholinoethanesulfonic acid</td><td>Sigma</td><td>M5287</td><td></td></tr><tr><td>photoinitiator</td><td>Irgacure&amp;nbsp;</td><td>2959</td><td></td></tr><tr><td>sodium chloride&amp;nbsp;</td><td>Sigma</td><td>S9888</td><td></td></tr><tr><td>chondroitin sulfate sodium salt&amp;nbsp;</td><td>Sigma</td><td>C9819</td><td></td></tr><tr><td>N-hydroxysuccinimide&amp;nbsp;</td><td>Sigma</td><td>130672</td><td></td></tr><tr><td>1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide hydrochloride</td><td>Sigma</td><td>E1769</td><td></td></tr><tr><td>2-aminoethyl methacrylate</td><td>Sigma</td><td>516155</td><td></td></tr><tr><td>dialysis tubing</td><td>Spectrum Laboratories&amp;nbsp;</td><td>132700</td><td></td></tr><tr><td>Collagenase 2</td><td>Worthington Biochemical&amp;nbsp;</td><td>LS004177</td><td></td></tr><tr><td>Collagenase 4</td><td>Worthington Biochemical&amp;nbsp;</td><td>LS004189</td><td></td></tr><tr><td>DMEM/F12 media</td><td>HyClone, Thermo Scientific&amp;nbsp;</td><td>SH3002301&amp;nbsp;</td><td></td></tr><tr><td>live/dead assay</td><td>Life Technologies</td><td>&lt;a href=&quot;https://www.lifetechnologies.com/order/catalog/product/L3224&quot;&gt;L3224&lt;/a&gt;</td><td></td></tr><tr><td>Tri reagent</td><td>Life Technologies</td><td>AM9738</td><td></td></tr><tr><td>Quant-iT PicoGreen dsDNA Assay Kit</td><td>Invitrogen</td><td>&lt;a href=&quot;https://www.lifetechnologies.com/order/catalog/product/P11496&quot;&gt;P11496&lt;/a&gt;</td><td></td></tr><tr><td>Sodium phosphate dibasic&amp;nbsp;</td><td>Sigma</td><td>S3264</td><td></td></tr><tr><td>Ethylenediaminetetraacetic acid disodium salt&amp;nbsp;</td><td>Sigma</td><td>E5134</td><td></td></tr><tr><td>L-Cysteine</td><td>Sigma</td><td>C1276</td><td></td></tr><tr><td>1,9-dimethylmethylene blue&amp;nbsp;</td><td>Sigma</td><td>341088</td><td></td></tr><tr><td>Instruments</td><td></td><td></td><td></td></tr><tr><td>UV light equipment - XX-15LW Bench Lamp, 365 nm</td><td>UVP</td><td>95-0042-07</td><td></td></tr><tr><td>Instron 5944 testing system&amp;nbsp;</td><td>Instron Corporation</td><td>E5940</td><td></td></tr></tbody></table>

3d hydrogel scaffolds for articular chondrocyte culture and cartilage generation

Human articular cartilage is highly susceptible to damage and has limited self-repair and regeneration potential. Cell-based strategies to engineer cartilage tissue offer a promising solution to repair articular cartilage. To select the optimal cell source for tissue repair, it is important to develop an appropriate culture platform to systematically examine the biological and biomechanical differences in the tissue-engineered cartilage by different cell sources. Here we applied a three-dimensional (3D) biomimetic hydrogel culture platform to systematically examine cartilage regeneration potential of juvenile, adult, and osteoarthritic (OA) chondrocytes. The 3D biomimetic hydrogel consisted of synthetic component poly(ethylene glycol) and bioactive component chondroitin sulfate, which provides a physiologically relevant microenvironment for in vitro culture of chondrocytes. In addition, the scaffold may be potentially used for cell delivery for cartilage repair in vivo. Cartilage tissue engineered in the scaffold can be evaluated using quantitative gene expression, immunofluorescence staining, biochemical assays, and mechanical testing. Utilizing these outcomes, we were able to characterize the differential regenerative potential of chondrocytes of varying age, both at the gene expression level and in the biochemical and biomechanical properties of the engineered cartilage tissue. The 3D culture model could be applied to investigate the molecular and functional differences among chondrocytes and progenitor cells from different stages of normal or aberrant development.

Idrogel bioattivi contenenti PEG e frazioni CS (Figura 1) rappresentano una piattaforma ideale per la cultura e la maturazione dei condrociti articolari umani 2,3,5,7. I condrociti di diverse epoche e stati patologici possono essere coltivati ​​con il metodo descritto ed analizzati per la loro fenotipo, espressione genica e proprietà biochimiche e meccaniche del tessuto cartilagineo generato. Tre campioni chondrocyte, juvenile- 6 mesi, adulto-34 anni e osteoarthritic- 74 anni, sono state raccolte dopo 3 settimane di coltura in 3D idrogel biomimetici. Analisi dell&#39;espressione genica di condrociti normali, sia giovani che adulti, hanno mostrato un aumento dell&#39;espressione dei geni COL2A1 e COL6A1 condrociti. Al contrario, condrociti malate mostrato una diminuzione drammatica COL2A1 mantenendo l&#39;espressione di Col6a1 (Figura 2) mostra una perdita di fenotipo condrogenica pur essendo coltivate in un ambiente biomimetico favorevole. Gli idrogel CS-PEG servono anche come un ambiente dinamico per i condrociti a proliferare, digerire la matrice preesistente di PEG e CS e depositano la loro matrice pericellulare e extracellulare, i principali componenti del tessuto cartilagineo maturo. Alla luce di queste capacità, espansione di condrociti dopo 3 settimane di coltura in vitro può essere stimato per la quantificazione del DNA con il colorante PicoGreen. Analisi comparativa dei tre gruppi di cellule mostrano che la densità cellulare di giovani e adulti popolazioni è rimasto invariato mentre condrociti OA hanno mostrato una diminuzione drammatica rispetto al giorno 1 di cultura. Stata anche osservata una perdita del contenuto di DNA per OA ma non altre condrociti suggerendo possibile morte delle cellule durante la coltura a lungo termine (Figura 3). La matrice secreta è stato quantificato come contenuto solfato-GAG per DMMB test-dye vincolante nella fase punto finale dopo 3 settimane di culture. Contenuto GAG è normalizzata per il peso umido del idrogel come recorded prima della digestione enzimatica e il contributo acellulare viene sottratto. Come mostrato in figura 4, condrociti depositato un&#39;analoga quantità significativa di GAG per 3 settimane di coltura in idrogel 3D. La presenza di un ponteggio fisica consente la valutazione delle proprietà biomeccaniche dei campioni attraverso unconfined prove di compressione 2,3. Mentre idrogel acellulari subiscono una diminuzione della moduli compressione, costrutti cellulari carichi mantenuti i moduli di compressione dopo 3 settimane in coltura (Figura 4). Il fenotipica, analisi biochimiche e biomeccaniche qui descritte sono quindi utili per valutare e comprendere le potenzialità di diverse popolazioni di condrociti per l&#39;ingegneria cartilagine. <img alt="Figura 1" src="/files/ftp_upload/53085/53085fig1.jpg" /> Figura 1. PEG-CS idrogel biomimetici per 3D condrociti cultura. condrociti sono risospesi in una miscela contenente poli (glicole etilenico diacrilato) (PEGDA) e condroitin solfato-metacrilato (CS-MA) e colato nello stampo gel cilindrica su misura. Dopo l&#39;esposizione ai raggi UV, solidificati gel sono raccolti dagli stampi e vitalità cellulare è valutata mediante colorazione morto dal vivo 24 ore post-incapsulamento. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53085/53085fig1large.jpg" target="_blank">Cliccate qui per vedere una versione più grande di questa figura.</a> <img alt="Figura 2" src="/files/ftp_upload/53085/53085fig2.jpg" /> Figura 2. Espressione dei geni condrogeniche in condrociti umani coltivati ​​in 3D idrogel biomimetici. Espressione genica quantitativa di marker cartilagine COL2A1 e Col6a1 da giovani, adulti e OA condrociti dopo 3 settimane di coltura in 3D idrogel biomimetici. I valori sono normalizzati a livello di espressione genica a giorno 1. Errore bars rappresentano media ± SD. * p &lt;0,05 come determinato da un test t Student a due code. Modificato da Smeriglio e coll. 2 <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53085/53085fig2large.jpg" target="_blank">Cliccate qui per vedere una versione più grande di questa figura.</a> <img alt="Figura 3" src="/files/ftp_upload/53085/53085fig3.jpg" /> Figura 3. contenuto di DNA in condrociti umani coltivati ​​in idrogel biomimetici 3D. Quantificazione del DNA da PicoGreen test in giovani, adulti e OA condrociti dopo 3 settimane di coltura in 3D idrogel biomimetici. I valori sono normalizzati a livello del DNA a giorno 1. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53085/53085fig3large.jpg" target="_blank">Clicca qui per vedere una versione più grande di questa figura.</a> <img alt="Figura 4" src="/files/ftp_upload/53085/53085fig4.jpg" /> &lt;br /&gt; Figura 4. Misurazione del contenuto di GAG e test di compressione non confinato di condrociti umani in giorno 1 e dopo 3 settimane di cultura in 3D idrogel biomimetici. (A) GAG quantificazione mediante test DMMB in condrociti al giorno 1 e dopo 3 settimane di cultura idrogel biomimetici 3D. I valori sono normalizzati a bagnare peso (ww) ed espressi in mg / g. (B) modulo di compressione (kPa) di acellulari e cellulari carichi di idrogel a giorno 1 e dopo 3 settimane di cultura in 3D idrogel biomimetici. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53085/53085fig4large.jpg" target="_blank">Clicca qui per vedere una versione più grande di questa figura.</a>

Watch this Scientific Journal Video about 3D Hydrogel Scaffolds for Articular Chondrocyte Culture and Cartilage Generation at JoVE.com

3D Hydrogel Scaffolds for Articular Chondrocyte Culture and Cartilage Generation

Cartilage repair represents an unmet medical challenge and cell-based approaches to engineer human articular cartilage are a promising solution. Here, we describe three-dimensional (3D) biomimetic hydrogels as an ideal tool for the expansion and maturation of human articular chondrocytes.

3D Hydrogel Ponteggi per articolare condrociti, Cultura e Cartilagine Generation

Human articular cartilage is highly susceptible to damage and has limited self-repair and regeneration potential. Cell-based strategies to engineer ...

3d-hydrogel-scaffolds-for-articular-chondrocyte-culture-cartilage

Nanyang Technological University

Research

JoVE Journal

Bioengineering

19.9K Views.  Stanford University. Cartilage repair represents an unmet medical challenge and cell-based approaches to engineer human articular cartilage are a promising solution. Here, we describe three-dimensional (3D) biomimetic hydrogels as an ideal tool for the expansion and maturation of human articular chondrocytes. 

Video: 3D Hydrogel Scaffolds for Articular Chondrocyte Culture and Cartilage Generation

Preparation of Chitosan-based Injectable Hydrogels and Its Application in 3D Cell Culture

The protocol presents a facile, efficient, and versatile method to prepare chitosan-based hydrogels using dynamic imine chemistry. The hydrogel is prepared by mixing solutions of glycol chitosan with a synthesized benzaldehyde terminated polymer gelator, and hydrogels are efficiently obtained in several minutes at room temperature. By varying ratios between glycol chitosan, polymer gelator, and water contents, versatile hydrogels with different gelation times and stiffness are obtained. When damaged, the hydrogel can recover its appearances and modulus, due to the reversibility of the dynamic imine bonds as crosslinkages. This self-healable property enables the hydrogel to be injectable since it can be self-healed from squeezed pieces to an integral bulk hydrogel after the injection process. The hydrogel is also multi-responsive to many bio-active stimuli due to different equilibration statuses of the dynamic imine bonds. This hydrogel was confirmed as bio-compatible, and L929 mouse fibroblast cells were embedded following standard procedures and the cell proliferation was easily assessed by a 3D cell cultivation process. The hydrogel can offer an adjustable platform for different research where a physiological mimic of a 3D environment for cells is profited. Along with its multi-responsive, self-healable, and injectable properties, the hydrogels can potentially be applied as multiple carriers for drugs and cells in future bio-medical applications.

Here we describe a facile preparation of chitosan-based injectable hydrogels using dynamic imine chemistry. Methods to adjust the hydrogel&#8217;s mechanical strength and its application in 3D cell culture are presented.

Preparazione di idrogeli iniettabili a base di chitosano e la sua applicazione nella coltura cellulare 3D

The protocol presents a facile, efficient, and versatile method to prepare chitosan-based hydrogels using dynamic imine chemistry. The hydrogel is ...

Ricerca

Chimica

Human Cartilage Tissue Fabrication Using Three-dimensional Inkjet Printing Technology

Bioprinting, which is based on thermal inkjet printing, is one of the most attractive enabling technologies in the field of tissue engineering and regenerative medicine. With digital control&#160;cells, scaffolds, and growth factors can be precisely deposited to the desired two-dimensional (2D) and three-dimensional (3D) locations rapidly. Therefore, this technology is an ideal approach to fabricate tissues mimicking their native anatomic structures. In order to engineer cartilage with native zonal organization, extracellular matrix composition (ECM), and mechanical properties, we developed a bioprinting platform using a commercial inkjet printer with simultaneous photopolymerization capable for 3D cartilage tissue engineering. Human chondrocytes suspended in poly(ethylene glycol) diacrylate (PEGDA) were printed for 3D neocartilage construction via layer-by-layer assembly. The printed cells were fixed at their original deposited positions, supported by the surrounding scaffold in simultaneous photopolymerization. The mechanical properties of the printed tissue were similar to the native cartilage. Compared to conventional tissue fabrication, which requires longer UV exposure, the viability of the printed cells with simultaneous photopolymerization was significantly higher. Printed neocartilage demonstrated excellent glycosaminoglycan (GAG) and collagen type II production, which was consistent with gene expression. Therefore, this platform is ideal for accurate cell distribution and arrangement for anatomic tissue engineering.

The methods described in this paper show how to convert a commercial inkjet printer into a bioprinter with simultaneous UV polymerization. The printer is capable of constructing 3D tissue structure with cells and biomaterials. The study demonstrated here constructed a 3D neocartilage.

Umana Cartilagine Tessuto Fabrication Uso tridimensionale Tecnologia Inkjet Printing

Bioprinting, which is based on thermal inkjet printing, is one of the most attractive enabling technologies in the field of tissue engineering and ...

Bioingegneria

Layered Alginate Constructs: A Platform for Co-culture of Heterogeneous Cell Populations

Many load bearing tissues possess structurally and functionally distinct regions, typically accompanied by different cell phenotypes with differential mechanosensing characteristics. Engineering and analysis of these tissue types remain a challenge. Layered hydrogel constructs provide an opportunity for investigating the interactions among multiple cell populations within single constructs. Alginate hydrogels are both biocompatible and allow for easy isolation of cells after experimentation. Here, we describe a method for the development of small sized dual layered alginate hydrogel discs. This process maintains high cell viability of human mesenchymal stem cells during the formation process and these layered discs can withstand unconfined cyclic compression, commonly used for stimulation of hMSCs undergoing chondrogenesis. These layered constructs can potentially be scaled up to include additional levels, and also be used to segregate cell populations initially after layering. This dual layer alginate hydrogel culture platform can be used for many different applications including engineering and analysis of cells of load bearing tissues and co-cultures of other cell types.

Engineering and analysis of load bearing tissues with heterogeneous cell populations are still a challenge. Here, we describe a method for creating bi-layered alginate hydrogel discs as a platform for co-culture of diverse cell populations within one construct.

Layered alginato costrutti: Una piattaforma per la cooperazione culturale delle popolazioni cellulari eterogenee

Many load bearing tissues possess structurally and functionally distinct regions, typically accompanied by different cell phenotypes with differential ...

3D Magnetic Stem Cell Aggregation and Bioreactor Maturation for Cartilage Regeneration

Cartilage engineering remains a challenge due to the difficulties in creating an in vitro functional implant similar to the native tissue. An approach recently explored for the development of autologous replacements involves the differentiation of stem cells into chondrocytes. To initiate this chondrogenesis, a degree of compaction of the stem cells is required; hence, we demonstrated the feasibility of magnetically condensing cells, both within thick scaffolds and scaffold-free, using miniaturized magnetic field sources as cell attractors. This magnetic approach was also used to guide aggregate fusion and to build scaffold-free, organized, three-dimensional (3D) tissues several millimeters in size. In addition to having an enhanced size, the tissue formed by magnetic-driven fusion presented a significant increase in the expression of collagen II, and a similar trend was observed for aggrecan expression. As the native cartilage was subjected to forces that influenced its 3D structure, dynamic maturation was also performed. A bioreactor that provides mechanical stimuli was used to culture the magnetically seeded scaffolds over a 21-day period. Bioreactor maturation largely improved chondrogenesis into the cellularized scaffolds; the extracellular matrix obtained under these conditions was rich in collagen II and aggrecan. This work outlines the innovative potential of magnetic condensation of labeled stem cells and dynamic maturation in a bioreactor for improved chondrogenic differentiation, both scaffold-free and within polysaccharide scaffolds.

Chondrogenesis from stem cells requires fine tuning the culture conditions. Here, we present a magnetic approach for condensing cells, an essential step to initiate chondrogenesis. In addition, we show that dynamic maturation in a bioreactor applies mechanical stimulation to the cellular constructs and enhances cartilaginous extracellular matrix production.

3D Stem magnetica cellulare Aggregazione e bioreattore maturazione per la cartilagine Regeneration

Cartilage engineering remains a challenge due to the difficulties in creating an in vitro functional implant similar to the native tissue. An approach ...

Culturing Mammalian Cells in Three-dimensional Peptide Scaffolds

A useful technique for culturing cells in a self-assembling nanofiber three-dimensional (3D) scaffold is described. This culture system recreates an environment that closely mimics the structural features of non-polarized tissue. Furthermore, the particular intrinsic nanofiber structure of the scaffold makes it transparent to visual light, which allows for easy visualization of the sample under microscopy. This advantage was largely used to study cell migration, organization, proliferation, and differentiation and thus any development of their particular cellular function by staining with specific dyes or probes. Furthermore, in this work, we describe the good performance of this system to easily study the redifferentiation of expanded human articular chondrocytes into cartilaginous tissue. Cells were encapsulated into self-assembling peptide scaffolds and cultured under specific conditions to promote chondrogenesis. Three-dimensional cultures showed good viability during the 4 weeks of the experiment. As expected, samples cultured with chondrogenic inducers (compared to non-induced controls) stained strongly positive for toluidine blue (which stains glycosaminoglycans (GAGs) that are highly present in cartilage extracellular matrix) and expressed specific molecular markers, including collagen type I, II and X, according to Western Blot analysis. This protocol is easy to perform and can be used at research laboratories, industries and for educational purposes in laboratory courses.

Here, we present a protocol to obtain 3D-culture systems in self-assembling peptide scaffolds to promote the differentiation of dedifferentiated human articular chondrocytes into cartilage-like tissue.

Coltura di cellule di mammifero in scaffold tridimensionale Peptide

A useful technique for culturing cells in a self-assembling nanofiber three-dimensional (3D) scaffold is described. This culture system recreates an ...

A 3D System for Culturing Human Articular Chondrocytes in Synovial Fluid

Cartilage destruction is a central pathological feature of osteoarthritis, a leading cause of disability in the US. Cartilage in the adult does not regenerate very efficiently in vivo; and as a result, osteoarthritis leads to irreversible cartilage loss and is accompanied by chronic pain and immobility 1,2. Cartilage tissue engineering offers promising potential to regenerate and restore tissue function. This technology typically involves seeding chondrocytes into natural or synthetic scaffolds and culturing the resulting 3D construct in a balanced medium over a period of time with a goal of engineering a biochemically and biomechanically mature tissue that can be transplanted into a defect site in vivo 3-6. Achieving an optimal condition for chondrocyte growth and matrix deposition is essential for the success of cartilage tissue engineering. 
 In the native joint cavity, cartilage at the articular surface of the bone is bathed in synovial fluid. This clear and viscous fluid provides nutrients to the avascular articular cartilage and contains growth factors, cytokines and enzymes that are important for chondrocyte metabolism 7,8. Furthermore, synovial fluid facilitates low-friction movement between cartilaginous surfaces mainly through secreting two key components, hyaluronan and lubricin 9 10. In contrast, tissue engineered cartilage is most often cultured in artificial media. While these media are likely able to provide more defined conditions for studying chondrocyte metabolism, synovial fluid most accurately reflects the natural environment of which articular chondrocytes reside in.
 Indeed, synovial fluid has the advantage of being easy to obtain and store, and can often be regularly replenished by the body. Several groups have supplemented the culture medium with synovial fluid in growing human, bovine, rabbit and dog chondrocytes, but mostly used only low levels of synovial fluid (below 20&#37;) 11-25. While chicken, horse and human chondrocytes have been cultured in the medium with higher percentage of synovial fluid, these culture systems were two-dimensional 26-28. Here we present our method of culturing human articular chondrocytes in a 3D system with a high percentage of synovial fluid (up to 100&#37;) over a period of 21 days. In doing so, we overcame a major hurdle presented by the high viscosity of the synovial fluid. This system provides the possibility of studying human chondrocytes in synovial fluid in a 3D setting, which can be further combined with two other important factors (oxygen tension and mechanical loading) 29,30 that constitute the natural environment for cartilage to mimic the natural milieu for cartilage growth. Furthermore, This system may also be used for assaying synovial fluid activity on chondrocytes and provide a platform for developing cartilage regeneration technologies and therapeutic options for arthritis.

A 3D system of culturing human articular chondrocytes in high levels of synovial fluid is described. Synovial fluid reflects the most natural microenvironment for articular cartilage, and can be easily obtained and stored. This system thus can be used for studying cartilage regeneration and for screening therapeutics for treating arthritis.

Un sistema 3D per condrociti articolari umani in coltura liquido sinoviale

Cartilage destruction is a central pathological feature of osteoarthritis, a leading cause of disability in the US. Cartilage in the adult does not ...

Biologia

Mechanical Stimulation of Chondrocyte-agarose Hydrogels

Articular cartilage suffers from a limited repair capacity when damaged by mechanical insult or degraded by disease, such as osteoarthritis. To remedy this deficiency, several medical interventions have been developed. One such method is to resurface the damaged area with tissue-engineered cartilage; however, the engineered tissue typically lacks the biochemical properties and durability of native cartilage, questioning its long-term survivability. This limits the application of cartilage tissue engineering to the repair of small focal defects, relying on the surrounding tissue to protect the implanted material. To improve the properties of the developed tissue, mechanical stimulation is a popular method utilized to enhance the synthesis of cartilaginous extracellular matrix as well as the resultant mechanical properties of the engineered tissue. Mechanical stimulation applies forces to the tissue constructs analogous to those experienced in vivo. This is based on the premise that the mechanical environment, in part, regulates the development and maintenance of native tissue1,2. The most commonly applied form of mechanical stimulation in cartilage tissue engineering is dynamic compression at physiologic strains of approximately 5-20% at a frequency of 1 Hz1,3. Several studies have investigated the effects of dynamic compression and have shown it to have a positive effect on chondrocyte metabolism and biosynthesis, ultimately affecting the functional properties of the developed tissue4-8. In this paper, we illustrate the method to mechanically stimulate chondrocyte-agarose hydrogel constructs under dynamic compression and analyze changes in biosynthesis through biochemical and radioisotope assays. This method can also be readily modified to assess any potentially induced changes in cellular response as a result of mechanical stimuli.

The biosynthesis of cartilaginous extracellular matrix by chondrocytes can be affected by application of mechanical stimuli. This method describes the technique of applying dynamic compressive strains to chondrocytes encapsulated in 3D constructs and the evaluation of induced changes in chondrocyte metabolism.

La stimolazione meccanica di condrociti-agarosio idrogel

Articular cartilage suffers from a limited repair capacity when damaged by mechanical insult or degraded by disease, such as osteoarthritis. To remedy ...

Creation of a Knee Joint-on-a-Chip for Modeling Joint Diseases and Testing Drugs

The high prevalence of debilitating joint diseases like osteoarthritis (OA) poses a high socioeconomic burden. Currently, the available drugs that target joint disorders are mostly palliative. The unmet need for effective disease-modifying OA drugs (DMOADs) has been primarily caused by the absence of appropriate models for studying the disease mechanisms and testing potential DMOADs. Herein, we describe the establishment of a miniature synovial joint-mimicking microphysiological system (miniJoint) comprising adipose, fibrous, and osteochondral tissue components derived from human mesenchymal stem cells (MSCs). To obtain the three-dimensional (3D) microtissues, MSCs were encapsulated in photocrosslinkable methacrylated gelatin before or following differentiation. The cell-laden tissue constructs were then integrated into a 3D-printed bioreactor, forming the miniJoint. Separate flows of osteogenic, fibrogenic, and adipogenic media were introduced to maintain the respective tissue phenotypes. A commonly shared stream was perfused through the cartilage, synovial, and adipose tissues to enable tissue crosstalk. This flow pattern allows the induction of perturbations in one or more of the tissue components for mechanistic studies. Furthermore, potential DMOADs can be tested via either &#34;systemic administration&#34; through all the medium streams or &#34;intraarticular administration&#34; by adding the drugs to only the shared &#34;synovial fluid&#34;-simulating flow. Thus, the miniJoint can serve as a versatile in vitro platform for efficiently studying disease mechanisms and testing drugs in personalized medicine.

We provide detailed methods for generating four types of tissues from human mesenchymal stem cells, which are used to recapitulate the cartilage, bone, fat pad, and synovium in the human knee joint. These four tissues are integrated into a customized bioreactor and connected through microfluidics, thus generating a knee joint-on-a-chip.

Creazione di un ginocchio joint-on-a-chip per la modellazione delle malattie articolari e la sperimentazione di farmaci

The high prevalence of debilitating joint diseases like osteoarthritis (OA) poses a high socioeconomic burden. Currently, the available drugs that target ...

Synthesis of Decellularized Cartilage Extracellular Matrix Hydrogels

Decellularized cartilage extracellular matrix (DC-ECM) hydrogels are promising biomaterials for tissue engineering and regenerative medicine due to their biocompatibility and ability to mimic natural tissue properties. This protocol aims to produce DC-ECM hydrogels that closely mimic the native ECM of cartilage tissue. The protocol involves a combination of physical and chemical disruption and enzymatic digestion to remove the cellular material while preserving the structure and composition of the ECM. The DC-ECM is cross-linked using a chemical agent to form a stable and biologically active hydrogel. The DC-ECM hydrogel has excellent biological activity, spatial structure, and biological induction function, as well as low immunogenicity. These characteristics are beneficial in promoting cell adhesion, proliferation, differentiation, and migration and for creating a superior microenvironment for cell growth. This protocol provides a valuable resource for researchers and clinicians in the field of tissue engineering. Biomimetic hydrogels can potentially enhance the development of effective tissue engineering strategies for cartilage repair and regeneration.

This paper introduces a new method for the synthesis of decellularized cartilage extracellular matrix (DC-ECM) hydrogels. DC-ECM hydrogels have excellent biocompatibility and provide a superior microenvironment for cell growth. Therefore, they can be ideal cell scaffolds and biological delivery systems.

Sintesi di idrogel di matrice extracellulare della cartilagine decellularizzata

Decellularized cartilage extracellular matrix (DC-ECM) hydrogels are promising biomaterials for tissue engineering and regenerative medicine due to their ...

Generating Spheroids from Various Chondrocytes using Low-Adhesive Conditions under Gravity and Homemade Mini-Bioreactors

Cartilage repair in chronic joint diseases demands advanced cell-based therapies to regenerate damaged tissues effectively. This protocol provides a step-by-step method for differentiating induced pluripotent stem cells (iPSCs) into chondrocyte-based spheroids, supporting tissue engineering and cell therapy applications. The differentiation process is carefully structured to promote chondrogenic lineage commitment, beginning with iPSCs cultured in specific media that sequentially guide cells through critical stages of differentiation. Initially, iPSCs are expanded to reach optimal confluency before induction toward chondrogenic lineage using a series of defined media changes. By day 10, cells are transitioned to a chondrogenesis-promoting medium that enhances the formation of chondrocyte-like cells expressing key markers of mature chondrocytes. Further aggregation in 96-well agarose-coated plates leads to the formation of three-dimensional spheroids, which are then cultured in custom mini-bioreactors designed to simulate a microenvironment that encourages extracellular matrix (ECM) deposition. By enabling scalable production of chondrocyte spheroids that mimic native cartilage characteristics, this approach offers a promising, reproducible solution for developing cell-based treatments for cartilage defects, providing broad utility for clinical and research applications in musculoskeletal regenerative medicine.

This study describes a method for producing chondrocytic spheroids by aggregating cells into spheroids under low-adhesion conditions using gravity, followed by culturing the resulting spheroids in mini-bioreactors.

Generazione di sferoidi da vari condrociti utilizzando condizioni di bassa adesività per gravità e mini-bioreattori fatti in casa

Cartilage repair in chronic joint diseases demands advanced cell-based therapies to regenerate damaged tissues effectively. This protocol provides a ...