OBJECTIVE To produce tissue engineered cartilage by human articular chondrocytes in vitro for further use in in vivo manipulations for the treatment of cartilage defects.
METHODS Human articular chondrocytes were cultured in 0.5%, 1.0%, and 2.0% of alginate for up to four weeks. The optimal concentration of an alginate matrix for cell replication and for aggrecan synthesis by chondrocytes was determined. DNA content in the different culture conditions was measured after two and four weeks. Aggrecan synthesis rates and accumulation in the surrounding extracellular matrix were assessed by [35S]sulphate incorporation after the same periods of culture. To follow the outgrowth of chondrocytes from the alginate beads, chondrocytes were cultured for four weeks in 0.5 or 1.0% alginate surrounded by 0.25 or 0.5% fibrin gel. DNA content of each culture was measured after different culture periods. Finally, human chondrocytes in 1.0% alginate beads were embedded in 0.5% fibrin gel for eight weeks. Immunohistochemical analysis for aggrecan, type I and II collagen was performed weekly.
RESULTS At two weeks the DNA content in each culture significantly increased in 0.5 and 1.0% alginate cultures in comparison with baseline values. This increase continued until week 4 at the three alginate concentrations. Aggrecan synthesis at two weeks was highest in 0.5 and 1.0% alginate cell cultures. At four weeks aggrecan synthesis rates decreased independently of the alginate concentrations. Aggrecan mainly accumulated in the interterritorial matrix. Proliferation of chondrocytes in alginate and outgrowth of these cells in the surrounding fibrin gel were evident throughout the culture period. The accumulation of aggrecan and type II collagen around the cells, in alginate as well as in fibrin gel, gradually increased over the culture period. Type I collagen appeared after six weeks in alginate and in the surrounding fibrin.
CONCLUSION Human chondrocytes proliferate in this culture system, show an outgrowth into the surrounding fibrin, and synthesise a cartilage-like matrix for up to eight weeks.
- tissue engineering
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Defects in the joint surface can be classified as chondral and osteochondral lesions according to whether or not they penetrate into the subchondral bone. The repair of osteochondral lesions is transient and imperfect.1 In these lesions a fibrin clot originates from the bleeding subchondral bone. Into this three dimensional fibrin matrix mesenchymal cells can migrate and produce growth factors. Chondral lesions normally do not heal spontaneously in mature cartilage.2 ,3 Chondrocytes, synoviocytes, or other cells do not migrate into the chondral lesions in the absence of a pre-existing matrix.3 Absence of repair ultimately leads to degenerative changes in the affected joint.1
In experimental models attempts have been made to fill chondral lesions with biocompatible matrices, such as fibrin or collagen.3 ,4 In these conditions cartilage repair obviously depends on the number of cells migrating into the artificial matrix. The extracellular matrix production by the few cells migrating into a chondral lesion is insufficient to restore the defect.
Implantation of autologous5 or heterologous4 ,6 chondrocytes, periosteum,7and perichondrium8 ,9 has been used to fill chondral defects with a sufficient number of cells required to repair the cartilage. None of these methods has proved to be efficient because the original hyaline cartilage was replaced by fibrocartilaginous tissue which eventually degenerated or was lost during follow up.
Implantation of isolated chondrocytes encapsulated in different artificial scaffolds such as synthetic polymers (carbon fibre,10 polylactic acid, and polyglycolic acid11 ,12) or biological matrices (demineralised bone matrix,13 collagen,4 ,14 ,15hyaluronan,16 ,17 fibrin6 ,18) for chondral and osteochondral lesions has been reported. The artificial matrices should be biodegradable at the appropriate rate and biocompatible to serve as a scaffold for the colonisation by the cells. The chondrocytes should be able to multiply and maintain their original phenotype with the production of cartilage-specific matrix components such as aggrecan and type II collagen.
In this study the proliferation of human articular chondrocytes and their aggrecan synthesis rates were investigated at different concentrations of highly purified alginate, a linear polysaccharide composed of l-guluronic and d-mannuronic acid linked by β1,4 and α1,4 glucoside bonds. Human chondrocytes are known to maintain their original phenotype in this naturally derived matrix in in vitro long term cultures.19 An optimal aggrecan synthesis and cell proliferation is of crucial importance when considering the healing of cartilage lesions by implantation of chondrocytes in a temporary scaffold.
The phenotypic stability and cell proliferation of human articular chondrocytes cultured in alginate beads surrounded by a cell-free fibrin gel were then investigated over a period of eight weeks. Fibrin gel has been shown to provide sufficient support to chondrocytes, and to enhance cell proliferation and new matrix production, resulting in neochondrogenesis in short term cultures.6 ,18 ,20 ,21
These experiments could lead to a possible matrix in the future treatment of cartilage defects.
Material and methods
ISOLATION OF ARTICULAR CHONDROCYTES
Human articular chondrocytes were isolated as described elsewhere,22 ,23 with a few modifications. Briefly, human articular cartilage was obtained at necropsy from femoral condyles of different donors within 24 hours of death. All donors had died after a short illness. None of them had received corticosteroids or cytostatic drugs. Visually intact cartilage was harvested and prepared for culture. Cartilage removed from the femoral condyles was diced into small fragments, and the chondrocytes were isolated by sequential enzymatic digestion (hyaluronidase, pronase, and collagenase) of the extracellular matrix as described in detail.24
Isolated cells were then centrifuged for 10 minutes at 800 rpm, washed three times in Dulbecco's modification of Eagle's medium (DMEM) with 10% fetal calf serum (FCS), tested for viability (trypan blue exclusion test), and counted. More than 95% of the cells were usually viable after isolation.
CHONDROCYTE CULTURE IN ALGINATE BEADS
Chondrocyte cultures in alginate beads were prepared as described elsewhere,25 with some modifications. Chondrocytes obtained from a 27 year old woman, a 19 year old man, and a 51 year old man (donors 1, 2, and 3, respectively) were suspended in one volume double concentrated Hanks's balanced salts solution without calcium and magnesium (HBSS; Gibco) and carefully mixed with an equal volume of 1, 2, or 4% alginate (low viscosity, highly purified alginate fromMacrocystis pyrifera; Sigma) in HBSS, autoclaved for 15 minutes. The final cell concentration of chondrocytes was 5×106/ml in 0.5, 1, or 2% alginate. The chondrocyte/alginate suspension was then slowly dripped through a 23-gauge needle into a 102 mM calcium chloride solution. The beads were allowed to polymerise for 10 minutes at room temperature. The calcium chloride was then removed, and the beads were washed three times with 0.15 M sodium chloride. The chondrocytes in the alginate beads were cultured in a six well plate with 1×106 cells per culture (each well containing 20 alginate beads; ±50 000 chondrocytes per 10 μl bead) in an incubator at 37°C under 5% CO2. Four ml of DMEM with 10% FCS and 50 μg freshly dissolved ascorbate per ml were then added and replaced three times weekly. All experiments were performed in triplicate.
PROLIFERATION OF CHONDROCYTES IN ALGINATE SURROUNDED BY FIBRIN GEL
Alginate beads were maintained in culture in a fibrin gel in order to follow the proliferation of chondrocytes in the beads and outgrowth of these cells into the surrounding fibrin. A 5% fibrinogen solution containing 3000 Kallidinogenase Inhibitor Units of the fibrinolysis inhibitor aprotinin per ml (Tissucol; Immuno AG, Vienna, Austria) was diluted to 0.5% and 0.25% with HBSS. The fibrinogen solution was stirred until the fibrinogen was dissolved.
Chondrocytes from two donors, a 37 year old man and a 62 year old woman (donors 4 and 5), were encased in 0.5 or 1.0% alginate. Two hundred μl of 1.0% alginate beads was then immersed in 300 μl 0.25 or 0.5% fibrinogen solution, and 200 μl of the 0.5% beads was placed in 300 μl 0.25% fibrinogen. The fibrinogen was allowed to gel by adding 100 μl of a 100 IU/ml thrombin solution dissolved in 4.44 mg/ml CaCl2. Before application this thrombin solution was warmed to 37°C. It took one minute for the fibrinogen to form a fibrin gel. DMEM (1.5 ml) with 10% of FCS and 50 μg/ml of freshly dissolved ascorbate were used as nutrient medium and replaced three times weekly. One batch of chondrocytes from donors 4 and 5 was also cultured in 0.5% fibrin. Colonisation of the alginate/fibrin matrix was followed by DNA measurements.
ACCUMULATION OF EXTRACELLULAR MATRIX BY CHONDROCYTES CULTURED IN ALGINATE SURROUNDED BY FIBRIN GEL
Chondrocytes cultures were made in 1.0% alginate surrounded by 0.5% fibrin gel as described above. The deposition of aggrecan, type II and I collagen by the chondrocytes in the alginate/fibrin matrix was stained by immunohistochemistry. A series of cultures from a 53 year old man (donor 6) was started and at different times (3 days, 1, 2, 3, 4, 6, and 8 weeks) one culture was either mounted in Jung tissue freezing medium (Leica Instruments, Nussloch, Germany) and stored at −80°C, until used for further cryosections with immunohistochemistry, or embedded in paraffin for light microscopy.
35S LABELLED AGGRECAN SYNTHESIS BY CHONDROCYTES IN ALGINATE BEADS
Radioactive label (10 μCi/ml) was included in the incubation medium of the alginate beads during the last 48 hours of weeks 2 and 4 of culture. The medium of the cultures was then aspirated and the alginate beads were washed and dissolved in 3 ml of 55 mM sodium citrate pH 6.8, 0.15 M NaCl at 25°C for 10 minutes. The resulting suspension was centrifuged at 900 rpm for 10 minutes to separate cells with their cell associated matrix (CAM—the pellet26) from the constituents of the interterritorial matrix (ITM—the supernatant). The aggrecans of the CAM were further extracted by incubation for 48 hours in dissociative conditions with 4 M GuHCl in a 50 mM sodium acetate buffer pH 5.8,27 at 4°C in the presence of proteinase inhibitors: 0.1 M ε-amino-n-caproic acid, 0.01 M EDTA, 0.005 M benzamidine chloride, and 0.01 M phenylmethylsulphonyl fluoride.28 This solution was subsequently centrifuged for 10 minutes at 1000 rpm and the dissociated CAM aggrecans were recovered in the supernatant. The suspensions obtained (CAM and ITM) and the nutrient media were stored separately at −20°C for further analysis.
Spent culture media, CAM and ITM solutions were desalted using gel permeation chromatography through Sephadex G25 gels (Pharmacia, Uppsala, Sweden) in 0.067 M phosphate (K2HPO4/Na2HPO4) pH 6.8, containing 0.01 M Na2SO4 to separate the35S labelled aggrecans from free [35S]sulphate (35SO4). The eluted macromolecular fractions were counted for radioactivity. The radioactivity under the curves was related to the total incorporation of 35SO4 in aggrecans by the respective cultures. Aggrecan synthesis was expressed as pg SO4incorporated into aggrecans per 1×106 chondrocytes per hour.29
Chondrocyte proliferation in the different culture conditions was followed by measurement of the DNA content in the chondrocyte cultures. Initially, each culture contained approximately 1×106 ± 50 000 chondrocytes. From each donor three cultures were stored at −20°C at day 1 after having been placed in culture (start value), and after two and four weeks. DNA content in each culture was assayed as described30 using the enhancement of fluorescence of trisbenzimidazole (Hoechst 33258; Pharmacia Biotech Inc, San Francisco, CA, USA) when it binds to double stranded DNA.31
The alginate cultures were dissolved by adding 3 ml of 55 mM sodium citrate, pH 6.8. The alginate cultures surrounded by a fibrin gel were dissolved by incubation with 100 mg/100 ml trypsin (Sigma) and 20 mg/100 ml EDTA (UCB, Leuven, Belgium) in sodium citrate at 37°C for 24 hours. The solutions obtained were further sonicated for 30 seconds (MSE ultrasonicator, type 5.65; power set at 100 W). One and a half ml of the solubilised alginate or alginate/fibrin cultures was added to 1.5 ml of the Hoechst dye solution, and fluorescence was measured in a Hoefer dynaquant 200 fluorometer (Hoefer Pharmacia Biotech Inc), with double stranded calf thymus DNA (Sigma) in phosphate buffered saline (PBS) as a standard. The emission was measured at 460 nm for an excitation wavelength of 365 nm.
The alginate/fibrin cultures were mounted in Jung tissue freezing medium. Frozen sections of 30 μm were layered on Star Frost glass slides (Knittelgläser, Braunschweig, Germany) and used for immunohistochemistry. The sections were fixed for 10 minutes in acetone and incubated for 30 minutes with the following mouse antihuman monoclonal antibodies (mAbs): anti-aggrecan (clone 969D4D11; Biosource Europe SA, Nivelles, Belgium), anti-type I collagen (clone I-8H5; ICN Biomedicals, Aurora, USA), and anti-type II collagen (clone II-4C11; ICN Biomedicals). Final dilutions were 1:50, 1:100, and 1:100 of 1 mg/ml for aggrecan, type I and type II collagen, respectively. Before incubation with the mouse mAb for type I and II collagen, the sections were incubated with 2500 IU/ml hyaluronidase (bovine testicular hyaluronidase VI-S; Sigma) in PBS for 40 minutes at 37°C to expose the appropriate epitopes.32 Parallel sections were incubated with irrelevant isotype matched mAb as a negative control. After incubation with the mAb, the cryosections were rinsed with PBS and endogenous peroxidase was blocked with 1% hydrogen peroxide in distilled water. The sections were subsequently incubated for 15 minutes with a biotinylated antimouse secondary antibody, followed by 15 minutes with a streptavidin-peroxidase complex (LSAB+ Kit, Dako, Glostrup, Denmark). The colour reaction was developed with 3-amino-9-ethylcarbazole substrate (Dako) as chromogen. Finally, the sections were counterstained with haematoxylin. All incubations were carried out at room temperature and the sections were washed with PBS between all steps. Isotype matched immunostaining was performed on cryosections of normal human skin and cartilage to confirm specificity of the antibodies. The mAbs for type II collagen and aggrecan specifically stained the cartilage, whereas the mAb for type I collagen stained the dermis.
Counting of cell nuclei was performed in one microscopic field. The ratio of positive staining cells for the above mentioned mAbs to the total cell number was determined.
All experiments (aggrecan synthesis rates, DNA measurement, and ratio of positive staining cells for a given epitope) were carried out threefold. Mean values and one standard deviation (SD) were calculated. Statistical analysis was carried out by the unpaired two tailed Studentt test to determine whether variables were significantly different (p<0.05) in the respective experiments.
PROLIFERATION OF CHONDROCYTES AT DIFFERENT CONCENTRATIONS OF ALGINATE AT DIFFERENT POINTS OF TIME
At two weeks DNA content in each culture was significantly higher than at day 1 when chondrocytes were cultured in 0.5% alginate. This increase in proliferation, though less pronounced, was also seen in the 1.0 and 2.0% alginate cultures at two weeks. After four weeks in culture a significant increase in cell proliferation was seen at the three different alginate concentrations (fig 1).
PROLIFERATION OF CHONDROCYTES CULTURED IN ALGINATE BEADS SURROUNDED BY FIBRIN GEL
At two weeks DNA content in each culture was significantly increased in the four different culture conditions (table 1). An increase of 29%, 24%, 33%, and 17% for donor 4 and of 27%, 38%, 43%, and 22% for donor 5 was seen in the 1.0% alginate surrounded by 0.5% fibrin gel, the 1.0% alginate cultures surrounded by 0.25% fibrin gel, the 0.5% alginate surrounded by 0.25% fibrin gel, and in the chondrocytes cultured as a suspension in 0.25% fibrin gel, respectively. DNA content in each culture was not significantly different between the four culture conditions at two weeks.
At four weeks cell proliferation was more pronounced than at two weeks. Compared with the start values DNA content in each culture was increased by 101%, 144%, 110%, and 50% for donor 4 and by 98%, 112%, 89%, and 57% for donor 5 in the respective culture conditions. When the four culture conditions at four weeks were compared, cell proliferation was significantly more pronounced in the cultures where chondrocytes were cultured in alginate beads surrounded by fibrin gel.
AGGRECAN SYNTHESIS AT DIFFERENT CONCENTRATIONS OF ALGINATE AT TWO AND FOUR WEEKS
Figure 2 shows total aggrecan synthesis (CAM, ITM plus medium) at two and four weeks.
At two weeks the total aggrecan synthesis was most pronounced in 0.5% alginate cultures, though a significant difference with the 1.0% alginate cultures was not found in donors 1 and 3. At this time most of the newly synthesised aggrecan was retained in the ITM in the 1.0 and 2.0% alginate cultures. A major portion of the aggrecans diffused into the medium in the 0.5% alginate cultures at two weeks. The diffusion of newly synthesised aggrecans in the nutrient medium was less pronounced in higher concentrated alginate gels. The CAM contained 10–20% of the newly synthesised aggrecan at two weeks in the three culture conditions.
At four weeks the total aggrecan synthesis rates in 0.5% alginate cultures remained most pronounced. A decrease in aggrecan synthesis rates was seen in all 2.0% alginate cultures and in two of three donors for 1.0% alginate cultures. The proportion of newly synthesised aggrecan retained in the ITM remained most important in 1.0 and 2.0% alginate cultures. Absolute and relative amounts of newly synthesised aggrecans in the nutrient media decreased with increasing concentration of alginate. Absolute and relative amounts of newly synthesised aggrecans retained in the CAM showed a tendency to decrease in the four week cultures at the three alginate concentrations used.
Because the DNA proliferation and aggrecan synthesis rates were determined on cultures from the same donors (donors 1–3),35SO4 incorporation per μg DNA could be calculated (fig 3). No consistent differences were found between the three alginate concentrations used, either at two weeks or at four weeks. The aggrecan synthesis rates for each cell were decreased after four weeks in culture in comparison with two weeks.
IMMUNOHISTOCHEMISTRY OF LONG TERM CULTURES OF CHONDROCYTES IN ALGINATE SURROUNDED BY FIBRIN GEL
From the start of the cultures a marked presence of positive staining cells for aggrecan in alginate was seen (fig 4A). The staining was pericellular, close to the cell. In the surrounding fibrin gel some cells were already present, though no staining for aggrecan was seen in this matrix after three days of culture. The number of positive staining cells for aggrecan in alginate increased progressively during the first two weeks in culture. From then on the number of positive cells remained rather constant (table 2). The extracellular staining became slightly more profuse in the intercellular matrix. Positive cells in the surrounding fibrin gel appeared at two weeks (fig 4B). At this time aggrecans were mainly seen in the immediate surroundings of the cells. At four weeks aggrecan staining became pronounced in the distant matrix (fig 4C). At eight weeks a diffuse deposition of aggrecan could be detected throughout both artificial matrices (fig4D). The alginate scaffold was poorly preserved during histological processing of the cryosections. The maintenance of the alginate gel with newly synthesised aggrecans in the CAM and in the ITM could be seen in paraffin sections (fig5).
Type II collagen appeared progressively over the first weeks in culture, as shown in table 2 and figs 4A and B. The staining was seen close to the cell (figs 4A and B). Type II collagen deposition in the ITM in alginate could hardly be seen during the eight week culture owing to a problem with processing the cryosections. In the fibrin gel the ITM and the CAM were diffusely stained with increasing numbers of positively stained cells (fig 4C). At eight weeks, 72% of the cells in the fibrin gel were stained for type II collagen, with a marked staining of the intercellular matrix (fig 4D).
In the alginate gel as well as in the fibrin gel, less collagen staining was present for type I collagen than for type II collagen and aggrecan (table 2). A slight pericellular staining in the alginate and in the fibrin was seen from weeks 2 to 3 onwards (fig 4C). Percentages of positive staining cells increased to 21% in the alginate and to 9% in the fibrin gel at eight weeks of culture (fig 4D).
Natural repair of chondral and osteochondral lesions in adult mammals does not occur.1 ,3 These lesions initiate degenerative changes of the affected joint. A valuable technique to restore a defect in the articular surface is still non-existent. Various surgical techniques have been reported in animals and in humans, such as abrasion techniques,33microfracturing,34 slurry grafting,35periosteal,8 perichondral,9 and osteochondral grafting,36-38 stem cell39 or chondrocyte6 ,40 transplantation. The short term clinical results of some of these techniques have been promising, though microscopic evidence that the repair tissue consists of hyaline cartilage instead of fibrocartilaginous tissue has not been obtained. Extensive studies of chondrocyte metabolism and behaviour in different situations and matrices will provide the necessary knowledge to achieve optimal repair of cartilage tissue. At present, tissue engineering of cartilage seems promising. Autologous or allogenous chondrocytes have been cultured in biodegradable and biocompatible three dimensional matrices, where they proliferate and synthesise an extracellular matrix containing cartilage-specific molecules such as aggrecan and collagen type II. Implantation of isolated chondrocytes in collagen, hyaluronan, and fibrin matrices for the treatment of cartilage defects has been performed.4 ,6 ,15-17 Although none of these matrices offers mechanical stability just after their implantation, they gradually become populated by cells which produce an extracellular matrix that allows the scaffold to become more resistant to tensile and compressive forces.13 ,15 ,20 ,41 Our study focused on the suitability of alginate gel as a vehicle for chondrocyte transplantation.
One of the advantages of alginate is the possibility of investigating the different intercellular compartments surrounding the chondrocytes in vitro: the CAM and the ITM.42 Newly synthesised aggrecans spend only a short time in the CAM with a higher rate of aggrecan turnover than in the ITM, making the CAM more biologically active.43 The ITM forms the largest domain of the intercellular matrix. The alginate matrix is biocompatible and biodegradable.44-47
Cell replication was most prominent at the lowest alginate concentration. Aggrecan synthesis rates (for each cell) were not influenced by the concentration of the alginate, but the chondrocytes decreased their aggrecan synthesis rates over time, probably as a response to the increasing accumulation of matrix components.
Overall aggrecan synthesis per mass unit of alginate was affected by the concentration of the gel. Increasing total 35S incorporation rates reflected increasing cell numbers at decreasing alginate concentrations. However, the lower the alginate content in the beads the more newly synthesised aggrecans escaped from the gel, and this 35S material was recovered in the nutrient media.
The consistent proliferation of the chondrocytes in 0.5 and 1% alginate gels and a better equilibrium between immobilisation and escape of newly formed extracellular matrix products in the 1 and 2% alginate gels made us choose 1% of alginate for further experiments. Furthermore, handling and manipulation of 0.5% alginate without damaging the beads was difficult. The synthesis and accumulation of aggrecans per mass unit of alginate is a more relevant parameter because similar events will occur in a future implant.
Chondrocytes were then cultured in alginate beads surrounded by a fibrin gel for a period of eight weeks. Fibrin gel is malleable, biodegradable, and biocompatible.6 ,18 When used in an implantation procedure it would permit the temporary scaffold to adhere to the edges of the cartilage lesion, allowing transplant integration.48 ,49 During the eight week culture period an outgrowth from the alginate beads into the surrounding fibrin gel was seen. In vitro outgrowth of chondrocytes from alginate beads into the surrounding nutrient medium has been reported, with the formation of a monolayer in the culture dishes after some weeks.50Neither the alginate content of the beads nor the concentrations of fibrin gel influenced the outgrowth from the beads or the colonisation of the surrounding fibrin matrix over a four week period. Fibrin gel has been used as a matrix for chondrocytes in in vitro18and in vivo6 ,51 experiments. The cells proliferate and synthesise an extracellular matrix resembling hyaline cartilage as long as the cells are surrounded by fibrin.18 Subcutaneously implanted fibrin containing allogeneic chondrocytes in nude mice has been shown to stimulate cell proliferation, cell migration, and matrix synthesis, forming neocartilaginous tissue.20 Conversely, fibrin gel used as a temporary scaffold for chondrocytes in osteochondral lesions in sheep did not show much resemblance to hyaline cartilage after one year, though the authors questioned the histological criteria used in their study.6
A disintegration of fibrin gel has been reported, though this might be influenced by a fibrinolysis inhibitor—for example, aprotinin, by increasing the concentration of fibrinogen or by using an optimal concentration of chondrocytes per ml.21 ,47 We found that the fibrin did not dissolve over a period of eight weeks, so that chondrocytes migrating from the alginate into the fibrin remained surrounded by a matrix. Immunohistochemistry showed a strong presence of cells staining for aggrecan and type II collagen in alginate from one week up to eight weeks, and a progressive increase of outgrowing aggrecan and type II positive cells in the surrounding fibrin gel. Staining for both extracellular matrix compounds also showed diffusion of the newly synthesised molecules into the surrounding matrix. This was less apparent in alginate than in fibrin because during the washing and staining procedures of the cryosections, the integrity of the alginate matrix was not maintained. The intercellular space was better conserved in paraffin sections.
It was concluded that a neosynthesis of a cartilage-like matrix over a short period in in vitro culture of human articular chondrocytes had occurred in this culture system. Immunostaining showed the presence of slight amounts of type I collagen (up to 21% staining cells in alginate and 9% in fibrin) after 6–8 weeks in culture. In vitro culture periods of 6–12 months are necessary to mimic a repair as seen in cartilage lesions in rabbits, guineapigs, and other animals. To have the same repair mechanism as seen in humans an even longer in vitro culture period is probably useful. This culture period is not feasible in practice.
The two matrices described above allow the diffusion of macromolecules and other nutrient factors necessary for cell viability, proliferation, and extracellular matrix synthesis.52
Autologous chondrocytes for cartilage repair in humans are currently used in operative techniques. A limitation in the number of autologous chondrocytes available for these procedures, the dedifferentation during ex vivo propagation of the cells necessary to reach a sufficient number of cells, and the need for repeated surgery explain the interest in the transplantation of allogeneic chondrocytes, possibly obtained from a “tissue bank”. The results of this study show the feasibility of in vitro proliferation and synthesis of a cartilage-like matrix by human chondrocytes in bioengineered tissue. Tissue engineered cartilage by chondrocytes cultured in alginate has been reported.41 ,53 In these studies the biocompatibility of the gel was confirmed, though the experiments were performed on athymic mice in a vascular region. If alginate containing chondrocytes is placed in vascular tissue in animals with a normal immune system an immunological response would be expected. When it is used for repair of cartilage defects, immune or inflammatory responses are unlikely because of the avascular properties of this tissue.
The authors thank Carine Broddelez and Jenny Vermeersch for their invaluable technical expertise.
Grants: Bijzonder Onderzoeks Fonds: project No 011D2698; Fonds voor Wetenschappelijk Onderzoek: project No 3G13201.
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