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.

All experiments were performed in accordance with the Stanford University Human subjects&#8217; guidelines and approved Institutional Review Board protocol.
1. Articular Chondrocyte Isolation
<ol>
	<li>Obtain cartilage from tissue discarded during total knee arthroplasty and dissect as described previously 8.</li>
	<li>Visually select the medial or lateral femoral condyles of cartilage samples for smooth surfaces and make incision at the surface of the cartilage through a scalpel in order to remove 4-5 mm cartilage biopsies without affecting the subchondral bone.</li>
	<li>Isolate chondrocytes from the extracellular matrix by enzymatic dissociation of the tissue with O/N treatment with purified collagenase. Use 1:1 ratio of Collagenase II (125 U/ml) and Collagenase IV (160 U/ml) in chondrocyte growth media at 37 &#176;C.</li>
	<li>The following day, filter the digested tissue containing the dissociated cells through a 70 mm pore size Nylon mesh. Wash two times with 20 ml of DMEM/F12 and centrifuge at 600 x&#160;g for 5 min.</li>
	<li>Plate the isolated chondrocytes at a density of 1 x 106 cells/60 mm culture dish following re-suspension in DMEM/F12 supplemented with 10% Fetal Bovine Serum (FBS), 25 &#181;g/ml&#160;ascorbate, 2 mM L-glutamine, antimicrobials (100 U/ml&#160;penicillin, 100 &#181;g/ml&#160;streptomycin, and 0.25 &#181;g/ml&#160;fungizone). Keep the plates at 37 &#176;C and maintain the primary chondrocyte cultures as a high-density monolayer prior to encapsulation in biomimetic hydrogels.</li>
</ol>
2. Biomimetic Hydrogel Fabrication
NOTE: This method allows the synthesis of a biomimetic hydrogel containing poly(ethylene glycol diacrylate) (PEGDA, MW 5,000 g/mole), chondroitin sulfate-methacrylate (CS-MA) in DPBS. The addition of photoinitiator enables photoactivated crosslinking. The final hydrogel composition contains 7% weight/volume (w/v) of PEGDA, 3% w/v of CS-MA, and 0.05% w/v of photoinitiator.
<ol>
	<li>Synthesize CS-MA by functionalizing CS polymer with methacrylate groups.
	<ol>
		<li>Prepare buffered solution of 50 mM 2-morpholinoethanesulfonic acid (MES) and 0.5 M sodium chloride (NaCl) by dissolving 1.952 g of MES and 5.84 g of NaCl in 200 ml&#160;of deionized water (DiH2O). Dissolve 5 g of chondroitin sulfate sodium salt in the buffered solution.</li>
		<li>Add 0.532 g (4.62 mmol) N-hydroxysuccinimide (NHS) and 1.771 g (9.24 mmol) 1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide hydrochloride (EDC) (molar ratio of NHS:EDC = 1:2) to the solution and stir for 5 min.</li>
		<li>Add 0.765 g (4.62 mmol) 2-aminoethyl methacrylate (AEMA) (molar ratio of NHS:EDC:AEMA = 1:2:1) to the solution and maintain the reaction at RT for 24 hr.</li>
		<li>Purify the mixture by dialysis against deionized water (diH2O) for 4 days using dialysis tubing (12-14 kDa MWCO).</li>
		<li>Filter the purified solution through a 0.22 &#956;m filter and place the open tubes containing the solution in the desiccator and vacuum O/N. Ensure that all tubes are protected from light. Store the dissolved polymer at -20 &#176;C protected from light and moisture.</li>
	</ol>
	</li>
</ol>
3. Cell Encapsulation
<ol>
	<li>Autoclave the PCR film and cylindrical rods (for punching out the cell-laden 3D hydrogels) and sterilize the custom-made cylindrical gel mold by submersion in 0.2 &#181;m filtered 70% ethanol in tissue culture hood under UV light.</li>
	<li>Seal the bottom of the gel mold with autoclaved PCR film without air bubbles or gaps to prevent leaks. Keep it in a sterile 150 mm plate.</li>
	<li>The day prior to cell encapsulation in biomimetic hydrogel, dissociate the high-density chondrocyte monolayer with O/N treatment in Collagenase II and Collagenase IV solution. Use 125 U/ml for Collagenase II and 160 U/ml for Collagenase VI each in chondrocyte growth media at 37 &#176;C.</li>
	<li>Take a 50 ml tube and add 5% weight/volume (w/v) poly(ethylene glycol diacrylate) (PEGDA, MW=5,000 g/mole), 3% w/v chondroitin sulfate-methacrylate (CS-MA), and 0.05% w/v photoinitiator in DPBS. Vortex the tube to mix the solution and keep it aside. Protect the tube from light.</li>
	<li>Collect the dissociated cells in a 50 ml Falcon tube, count and centrifuge at 460 x g for 5 min. Aspirate all the media from the cells tube and add the above mixed gel material to re-suspend cells at a density of 15&#215;106 cells/ml. Mix it 30 times thoroughly while avoiding air bubbles formation.</li>
	<li>Pipette 72 &#181;l of the cell-hydrogel suspension or hydrogel alone into the custom-made cylindrical gel mold and Induce gelation through exposure to UV light (365 nm wavelength) at 3 mW/m2 for 5 min. Prepare some hydrogel solution with no cell content. Use these constructs as negative controls for the future biochemical and mechanical testing. Measure the intensity of the UV light with a UV intensity meter. To adjust intensity, change the distance between the UV light source and the hydrogel scaffold during gelation. 
	NOTE: Since the hydrogel contains CS, the acellular contribution is subtracted from the biochemical GAG content of the cell-laden hydrogels to represent only the cellular GAG.</li>
	<li>Use a scalpel to cut the film for easy peel off and carefully remove it. With the help of the cylindrical rods, push out the gel into a 6 well plate with 5 ml of sterile DPBS to wash off unpolymerized gel and loose cells.</li>
	<li>Culture the cell-laden hydrogels in 24 well plates containing 1.5 ml of chondrocyte growth media into each well. Use a disposable spatula to transfer the washed hydrogels into the well.</li>
	<li>Assess cell viability by live dead staining 24 hr post-encapsulation using a viability/cytotoxity kit. Culture the cell-laden hydrogels and the empty hydrogels for 3-6 weeks changing to fresh chondrocyte growth media every 2 days before harvesting for analyses.</li>
</ol>
4. RNA Extraction and Gene Expression Analyses
<ol>
	<li>Carefully aspirate the media and put sterile PBS 1X on the cell-laden as well as the empty control hydrogels.</li>
	<li>With the help of a sterile spatula, transfer each hydrogel to a clean 1.5 ml eppendorf tube and add 250 &#181;l of Tri-reagent to each tube. Follow manufacturer&#8217;s instructions to isolate RNA.</li>
	<li>After RNA isolation and quantification use 1 &#181;g of it from each sample and perform a reversed transcription into cDNA using the High Capacity cDNA Reverse Transcription Kit.</li>
	<li>For quantitative PCR use TaqMan Gene Expression Arrays for examination of the expression of your genes of interest. Normalize the gene expression levels internally to GAPDH.</li>
	<li>For the PCR conditions include a 2&#160;min incubation at 50 &#176;C to inactivate previous amplicons with uracil-DNA glycosylase, followed by a 10&#160;min incubation at 95 &#176;C to activate the Taq polymerase. Then perform forty cycles of PCR, consisting of 15 sec&#160;at 95 &#176;C, and 1 min&#160;at 60 &#176;C.</li>
</ol>
5. Biochemical Analyses
<ol>
	<li>For each cell-hydrogel constructs quantify DNA and sulfated glycosaminoglycan (sGAG) production as follow.</li>
	<li>Carefully aspirate the media and put sterile PBS 1X on the cell-laden as well as the empty control hydrogels. Weigh an empty tube and put the hydrogel inside after blotting it on tissue paper and record the weight or wet weight of the hydrogels.</li>
	<li>Freeze each hydrogel at -20 &#176;C in a separate 1.5 ml eppendorf tube for enzymatic digestion and later use an aliquot of the digested product to run Picogreen assay (for DNA) and Dimethyl-Methylene blue assay (for GAG).</li>
	<li>Prepare the papainase solution for enzymatic digestion of the hydrogels.
	<ol>
		<li>First prepare the PBE buffer by weighing out 7.1 g of Sodium phosphate dibasic (Na2HPO4) and 1.6 g of Ethylenediaminetetraacetic acid disodium salt (EDTA-Na2). Dissolve in 500 ml of dH2O, adjust the pH to 6.5 and filter the purified solution through a 0.22 mm filter.</li>
		<li>Dissolve 0.035 g of L-cysteine in 20 ml of PBE buffer. Filter the solution and 100 &#181;l of sterile papain enzyme.</li>
	</ol>
	</li>
	<li>When ready to perform the assays, take the tubes from -20 &#176;C and add 300 &#956;l of the ready papain solution to the frozen hydrogels. Crush the gel with a mortar and pestle and mix it well with the motor pestle.</li>
	<li>Bring the volume to 500 &#181;l with additional papain solution. Perform the same procedure for the control gels. Incubate at 60 &#176;C for 16 hr 3,9. The solution containing the digested hydrogel can therefore used for DNA and GAG quantification. Measure the DNA content using the Picogreen assay with Lambda phage DNA as standard following manufacturer&#8217;s protocol.</li>
	<li>Quantify the sulfated-GAG content using the 1,9-dimethylmethylene blue (DMMB) dye-binding assay with shark chondroitin sulfate as standard 10. Determine the GAG content by dividing the amount of GAG for the corresponding wet weight.</li>
</ol>
6. Mechanical Testing
<ol>
	<li>Perform unconfined compression tests using an Instron 5944 testing system fitted with a 10 N load cell.
	<ol>
		<li>After the desired days of in vitro culture, perform the compression test on the cell-hydrogel scaffold and the acellular control hydrogels.</li>
		<li>Submerge the specimens in a PBS bath at RT and compress at a rate of 1% strain/sec to a maximum strain of 15% 11,12 since the physiological strain experienced by cartilage tissue under loading condition has been reported to be 10-20% 13,14.</li>
	</ol>
	</li>
	<li>Create stress vs. strain curves and curve fit using a third order polynomial equation. Determine the compressive tangent modulus from the curve fit equation at strain values of 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.

As reported in this protocol, 3D hydrogels are able to maintain chondrocyte phenotype in culture, avoiding the process of cell dedifferentiation into fibrocartilage cells usually encountered with monolayer cultures 15. Moreover, long-term cultures of the chondrocytes- hydrogel construct revealed a favorable environment that maintains the intrinsic cell features associated with age and disease.
The use of a 3D biomimetic hydrogel has several advantages. First, the inclusion of chondroitin sulfate (CS), a major component found in articular cartilage, enable cells to degrade the hydrogel matrix by secreting chondroitinase and lay down newly synthesized cartilage extra-cellular matrix 5, 16. In addition, CS has been shown to have anti-inflammatory properties in the arthritic joint. The biomimetic hydrogel may also be used as a scaffolding material for cell delivery in cartilage repair, and may be chemically modified to facilitate better tissue-biomaterial integration 17,18.
The use of the PEG-CS hydrogels allows long-term cultures of chondrocytes and the evaluation of biochemical and mechanical properties. Here we show how this platform can be useful for the comparative analyses of various sources of differentiated chondrocytes in order to define the optimal cell type for cartilage engineering. Interestingly, chondrocytes encapsulated in hydrogels remain viable and proliferate according to their intrinsic abilities. The hydrogel composition supports, in fact, the growth of healthy juvenile and adult chondrocytes as shown in Figure 2. The composition and structure of the described hydrogels also promotes cartilage tissue formation as indicated by the deposition of a functional extracellular matrix assessed by glycosaminoglycan (GAG) quantification.
An additional advantage is that the chondrocyte-hydrogel constructs can be evaluated for the mechanical properties of the newly formed cartilage tissue. Note that the unconfined compression test should be performed on the acellular hydrogel for comparison. The hydrogels, in fact, have an intrinsic stiffness due to the rigidity of the CS moieties. Unconfined compression strain of 5-20% (at a strain rate 1%/s) can be applied for the mechanical testing of cartilage tissue 11,12 since the physiological strain experienced by cartilage tissue under loading condition has been reported to be 10-20% 13,14. The response of both cell-laden and acellular hydrogels to mechanical testing was evaluated at the culture end-point. In the described example above we observed a comparable stiffness of the constructs containing adult and juvenile chondrocytes in contrast to the lower stiffness of the constructs containing OA chondrocytes. Such mechanical properties of the cell-hydrogel construct allow the assessment of the functional properties of the formed tissue giving an in-depth analysis of the cell maturation ability.
In conclusion, the use of the 3D biomimetic hydrogels to study the potential of different chondrocyte population to generate cartilage tissue can be widely applied. Besides the in vitro studies described here, in vivo transplantation of the cell-laden constructs can be envisioned to study cell maturation and regenerative potential in the physiological context. Further modifications of the hydrogel platform with additional biomimetic factors can also be envisioned to optimize chondrocyte proliferation and maturation.

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.

Bioactive hydrogels containing PEG and CS moieties (Figure 1) represent an ideal platform for culture and maturation of human articular chondrocytes 2,3,5,7. Chondrocytes from different ages and disease states can be cultured with the described method and analyzed for their phenotype, gene expression and biochemical and mechanical properties of the cartilage tissue generated. Three chondrocyte samples, juvenile- 6 months, adult- 34 years and osteoarthritic- 74 years, were harvested after 3 weeks of culture in 3D biomimetic hydrogels. Gene expression analyses of normal chondrocytes, both juvenile and adult, showed an increase in the expression of the chondrocyte genes Col2a1 and Col6a1. On the contrary, diseased chondrocytes showed a dramatic decrease in Col2a1 while maintaining the expression of Col6a1 (Figure 2) showing a loss of chondrogenic phenotype despite being cultured in a favorable biomimetic environment.
The CS-PEG hydrogels also serve as a dynamic environment for the chondrocytes to proliferate, digest the pre-existing matrix of PEG and CS and deposit their pericellular and extracellular matrix, the main components of the mature cartilage tissue. Given these abilities, chondrocyte expansion after 3 weeks of in vitro culture can be estimated by quantification of DNA with the Picogreen dye. Comparative analysis of the three groups of cells show that the cell density of juvenile and adult populations was unchanged while OA chondrocytes exhibited a dramatic decrease compared to day 1 of culture. A loss of DNA content was also observed for OA but not other chondrocytes suggesting possible cell death during the long-term culture (Figure 3). The secreted matrix was quantified as sulfated-GAG content by DMMB dye-binding assay at the end point stage after 3 weeks of cultures. GAG content is normalized by the wet weight of the hydrogel as recorded before the enzymatic digestion and the acellular contribution is subtracted. As shown in Figure 4, chondrocytes deposited a similar significant amount of GAG during 3 weeks of culture in 3D hydrogels.
The presence of a physical scaffold allows the evaluation of biomechanical properties of the samples through unconfined compression tests 2,3. While acellular hydrogels undergo a decrease in the compressive moduli, cell-laden constructs maintained the compressive moduli after 3 weeks in culture (Figure 4). The phenotypic, biochemical and biomechanical analyses described here are therefore useful for evaluating and understanding the potential of different chondrocyte populations for engineering cartilage.
<img alt="Figure 1" src="/files/ftp_upload/53085/53085fig1.jpg" /> 
Figure 1.&#160;PEG-CS biomimetic hydrogels for 3D chondrocyte culture.&#160;Chondrocytes are resuspended in a mixture containing Poly(ethylene glycol diacrylate) (PEGDA) and chondroitin sulfate-methacrylate (CS-MA) and casted into the custom-made cylindrical gel mold. After UV exposure, solidified gels are collected from the molds and cell viability is assessed by live dead staining 24 hr post-encapsulation. <a href="https://www.jove.com/files/ftp_upload/53085/53085fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" src="/files/ftp_upload/53085/53085fig2.jpg" /> 
Figure 2.&#160;Expression of chondrogenic genes in human chondrocytes cultured in 3D biomimetic hydrogels.&#160;Quantitative gene expression of cartilage markers Col2a1 and Col6a1 by juvenile, adult and OA chondrocytes after 3 weeks of culture in 3D biomimetic hydrogels. Values are normalized to gene expression level at day 1. Error bars represent mean&#177; SD. p* &#60;0.05 as determined by a two-tailed Student t test. Modified from Smeriglio et al. 2 <a href="https://www.jove.com/files/ftp_upload/53085/53085fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" src="/files/ftp_upload/53085/53085fig3.jpg" /> 
Figure 3.&#160;DNA content in human chondrocytes cultured in 3D biomimetic hydrogels.&#160;DNA quantification by Picogreen assay in juvenile, adult and OA chondrocytes after 3 weeks of culture in 3D biomimetic hydrogels. Values are normalized to DNA level at day 1. <a href="https://www.jove.com/files/ftp_upload/53085/53085fig3large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" src="/files/ftp_upload/53085/53085fig4.jpg" /> 
Figure 4.&#160;GAG content measurement and unconfined compression test of human chondrocytes at day 1 and after 3 weeks of culture in 3D biomimetic hydrogels.&#160;(A) GAG quantification by DMMB assay in chondrocytes at day 1 and after 3 weeks of culture in 3D biomimetic hydrogels. Values are normalized to wet weight (w.w.) and expressed as &#181;g/g. (B) Compressive modulus (kPa) of acellular and cell-laden hydrogels at day 1 and after 3 weeks of culture in 3D biomimetic hydrogels. <a href="https://www.jove.com/files/ftp_upload/53085/53085fig4large.jpg" target="_blank">Please click here to view a larger version of this figure.</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.

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

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.

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

Chemistry

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.

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

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.

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.

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.

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.

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

Biology

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.

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.

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.

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.

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