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We report engineering of half-centimeter–sized bone constructs created in vitro using human adipose-derived stem cells (hASCs), decellularized bone scaffolds, and perfusion bioreactors. The hASCs are easily accessible, can be used in an autologous fashion, are rapidly expanded in culture, and are capable of osteogenic differentiation. hASCs from four donors were characterized for their osteogenic capacity, and one representative cell population was used for tissue engineering experiments. Culture-expanded hASCs were seeded on fully decellularized native bone scaffolds (4mm diameter×4mm thick), providing the necessary structural and mechanical environment for osteogenic differentiation, and cultured in bioreactors with medium perfusion. The interstitial flow velocity was set to a level necessary to maintain cell viability and function throughout the construct volume (400μm/s), via enhanced mass transport. After 5 weeks of cultivation, the addition of osteogenic supplements (dexamethasone, sodium-β-glycerophosphate, and ascorbic acid-2-phosphate) to culture medium significantly increased the construct cellularity and the amounts of bone matrix components (collagen, bone sialoprotein, and bone osteopontin). Medium perfusion markedly improved the distribution of cells and bone matrix in engineered constructs. In summary, a combination of hASCs, decellularized bone scaffold, perfusion culture, and osteogenic supplements resulted in the formation of compact and viable bone tissue constructs.
Skeletal defects due to trauma, tumors, infection, genetic diseases, and abnormal development often require bone transplantation. Following blood, this is the second most common tissue transplant, with 2.2 million grafting procedures performed annually worldwide. Because of the aging of the population, this number is expected to increase further in coming years. The preferred treatment option for bone repair is the use of autologous tissue, although the limited availability and donor site morbidity remain significant drawbacks to this method.1,2 Tissue engineering could provide autologous bone tissue grafts formed by cells cultured on scaffolds and thereby alleviate the shortage of donor tissue. Human sources of osteogenic cells, appropriate scaffolds, bioreactor culture systems, and subsequent functional integration with the host are among the critical components for engineering viable bone grafts.
Human cells from a variety of tissues have been shown to have osteogenic potential, including osteoblasts,3 mesenchymal stem cells (MSCs),4,5 skin, amniotic membrane, lungs,6 and adipose-derived stem cells (ASCs).7,8 Human ASCs (hASCs) were selected for our study because of the ease of access of adipose tissue, high yield per unit tissue volume, rapid cell proliferation, and the possibility of either autologous or allogeneic use.9 Osteogenic potential of these cells has been demonstrated in monolayer culture7,8 and on various scaffolds including collagen,10,11 akermanite,12 poly(dl-lactic-co-glycolic acid),13 and beta-tricalcium phosphate.12,14 Animal studies have shown new bone formation by hASCs implanted subcutaneously10,14–17 in calvarial defects18,19 and mandibular defects.20
A scaffold is generally designed to provide a stimulatory three-dimensional environment for tissue formation.11 A bone scaffold should be biocompatible and osteoinductive and have appropriate structural and mechanical properties.1 Osteogenesis of human MSCs (hMSCs) cultured on scaffolds was enhanced by the presence of extracellular bone matrix.21 Likewise, the implantation of engineered bone generated by the hMSCs enhanced bone healing in vivo when compared with the effects of either hMSC-seeded scaffold or scaffold alone.22 Fully decellularized bone scaffolds were used in our study because of their ideal molecular composition, structural properties, and mechanical properties, enabling bone development in vitro and immediate mechanical support following graft implantation into load-bearing areas. Osteoinductive molecules (e.g., collagen and bone morphogenic proteins) that are preserved within the organic phase are potent modulators of osteogenic differentiation.23,24 Scaffolds with pore sizes in the range of 200–900μm20,25–27 that mimic the structure of bone have been shown to enable cellular penetration, extracellular matrix production, and eventual blood vessel ingrowth.
In native bone, interstitial flow plays a major role in providing the exchange of nutrients, oxygen, and waste products with the metabolically active bone cells and it serves as a source of hydrodynamic shear that is an intrinsic component of the bone environment. In tissue engineering studies, medium perfusion enhanced the formation of bone from bone marrow-derived hMSCs.5,28–31 Short-term perfusion of the stromal vascular fraction of human adipose tissue improved osteogenic and vasculogenic capabilities of the cells implanted in vivo.32 When exposed to short-term fluid flow in parallel-plate flow chambers, ASCs responded in a similar fashion as bone cells.33,34 As longer periods are needed for differentiation into a mature osteoblastic phenotype,35 our study evaluated the effects of perfusion on ASC-based bone constructs for extended cultivation times.
We report here a promising novel approach for engineering bone tissue from hASCs cultured for 5 weeks on fully decellularized bone scaffolds in a perfusion bioreactor.
All protocols were reviewed and approved by the Pennington Biomedical Research Center Institutional Research Board. Liposuction aspirates from subcutaneous adipose tissue were obtained from four female donors (termed A, B, C, and D, without any identifiers) undergoing an elective procedure. hASCs were isolated from lipoaspirates using previously described methods36 and expanded in high-glucose Dulbecco's modified Eagle's medium (DMEM) supplemented with 10% fetal bovine serum (FBS), 1ng/mL basic fibroblast growth factor, and penicillin–streptomycin (1%). The cells were plated at a density of 5000cells/cm2 and expanded to the third passage that was used for all experiments performed in our study.
To test their osteogenic capacity, hASCs were plated at a density of 5000cells/cm2 and cultured in osteogenic medium consisting of high-glucose DMEM, FBS (10%), dexamethasone (100nM), sodium-β-glycerophosphate (10mM), ascorbic acid-2-phosphate (0.1mM), and penicillin–streptomycin (1%). Control medium for cultivation of undifferentiated cells consisted of high-glucose DMEM, FBS (10%), and penicillin–streptomycin (1%). After 1–4 weeks of culture, n=3–4 wells per condition and time points were assessed for alkaline phosphatase (AP), von Kossa staining, alizarin red, and DNA content.
Aliquots of 0.5×106 cells in suspension were centrifuged at 500g for 12min and incubated overnight to form round pellets of cells. Each pellet was cultured in a tube containing 1mL of the control medium or osteogenic medium, for up to 4 weeks. For evaluation, the pellets were fixed in 10% formalin, dehydrated with graded ethanol washes, embedded in paraffin, sectioned to 5μm, and mounted on glass slides. The sections were deparaffinized with Citrisolv (Fisher, Pittsburg, PA) and rehydrated with a graded series of ethanol washes. For von Kossa staining, the tissue sections were treated with 5% AgNO3 and exposed to a strong light for 30min to show mineral deposition, observed by black stain. Calcium and DNA contents were measured as described below.
Scaffolds were decellularized as in our previous studies.31 Briefly, trabecular bone pieces were cored from the carpometacarpal joints of young cows and washed with a high velocity stream of water to remove bone marrow. Scaffolds were further washed for 1h in phosphate-buffered saline (PBS) with 0.1% ethylenediamine tetraacetic acid (EDTA) at room temperature, followed by sequential washes in hypotonic buffer (10mM Tris and 0.1% EDTA) overnight at 4°C, in detergent (10mM Tris and 0.5% sodium dodecyl sulfate [SDS]) for 24h at room temperature, and in enzyme solution (50U/mL DNAse, 1U/mL RNAse, and 10mM Tris) for 3h at 37°C, to fully remove cellular material. Scaffolds were then rinsed in PBS, freeze-dried, and cut into 4mm diameter×4mm high cylindrical plugs. The densities of scaffolds were calculated based on the dry weights and exact dimensions. The scaffolds within the density range of 0.37–0.45mg/mm3 were selected for experiments and were sterilized in 70% ethanol.
A novel perfusion bioreactor system has been used for culturing hASCs on decellularized bone scaffolds.31 The culture medium (40mL per bioreactor) flowed through a central port at the bottom of the bioreactor vessel from where it was evenly distributed into six channels leading into the individual culture wells. One scaffold per well was press-fit within a layer of polydimethylsiloxane. The medium from all six wells was then collected into the reservoir above the culture wells, where it was equilibrated with respect to oxygen and pH in a humidified incubator and exited through the port at the side of the bioreactor. For medium recirculation, a multichannel digital peristaltic pump (Ismatec; Cole-Parmer, Vernon Hills, IL) was used. The flow rate (1.8mL/min, corresponding to the interstitial flow velocity of 400μm/s through the scaffolds) was chosen based on previous experiments.31
Culture-expanded hASCs were suspended in control medium using 1.5×106 cells in 40μL volume, and the cell suspension was added on the top of each blot-dried scaffold. The cell suspension was pipetted in and out, to enhance even distribution of cells within the scaffolds. After 15min in the incubator, the scaffolds were flipped and an additional 10μL of cell-free medium was added to the top to prevent them from drying out. This process was repeated four times, after which the seeded constructs were transferred into six-well plates and incubated in control medium for 2 days to allow the cells to attach. Subsequently, n=9 seeded scaffolds were used for evaluation of seeding efficiency; n=24 scaffolds were transferred into four perfusion bioreactors (six per bioreactor); and n=24 scaffolds were kept in static culture. Two types of medium (control and osteogenic) were used for both the static and bioreactor cultures.
The experimental groups were as follows: (1) static-control, (2) static-osteogenic, (3) perfused-control, and (4) perfused-osteogenic. In all groups, the culture medium was changed 50% twice weekly throughout the culture period. The scaffolds were harvested for assessments after 2 and 5 weeks of culturing. For DNA assays, n=3 constructs per experimental group and time point were harvested, and another n=3 constructs were used for histology, immunohistochemistry, scanning electron microscopy, and microcomputed tomography (μCT).
The cells cultured in monolayers were washed with PBS, and then 200μL of digestion buffer (10mM Tris, 1mM EDTA, 0.1% Triton X-100, 0.1mg/mL proteinase K) was added and a cell scraper was used to remove the cells from the well. Cell pellets and tissue constructs were also washed in PBS and placed in 500μL of digestion buffer in microcentrifuge tubes. All samples were incubated in digestion buffer overnight at 56°C. The supernatants were then drawn off and pipetted in duplicate in 96-well plates. Picogreen dye (Molecular Probes, Eugene, OR) was added to the samples in 1:1 ratio and read in a fluorescent plate reader (excitation 485nm and emission 528nm). A standard curve was prepared from a solution of salmon testes DNA (Molecular Probes). The conversion factor was obtained from initial studies to determine the DNA content of hASCs and corresponded to 5pg DNA/cell.
Cell pellets were extracted by 5% trichloroacetic acid (500μL per sample). O-Cresolphtalein complex was added (Calcium CPC LiquiColor Test®; Stanbio Laboratory, Boerne, TX), and the calcium content was determined spectrophotometrically at 550nm.
The constructs were cut in half, incubated with calcein AM (indicating live cells) and ethidium homodimer-1 (indicating dead cells) according to the manufacturer's protocol (LIVE/DEAD® Viability/Cytotoxicity Kit; Molecular Probes), and then observed and imaged on a confocal microscope. Optical slices were taken from the surface at 10μm intervals, up to the depth of 160μm, and then presented as a vertical projection.
The cells were harvested in 100μL of lysate buffer (PBS, 1% Triton X-100, 0.5% sodium deoxycholate, 0.1% SDS, 0.1mg/mL phenylmethylsulfonylfluoride, and 0.3% aprotinin), maintained on ice, and vortexed intermittently for 30min to break down the cell membranes. The extracts were removed and centrifuged and the supernatants were stored at −20°C. Fifty microliters of a sample was incubated with 50μL alkaline buffer and 50μL nitrophenyl-phosphate substrate solution in microcentrifuge tubes at 37°C for 15min. The reaction was stopped with 0.5N NaOH. The absorbance was read at 405nm and compared with a standard curve obtained from p-nitrophenol solutions of known concentrations.
The cultures were fixed in 70% ethanol for 1h at 4°C, rinsed three times with distilled water, and stained in 2% alizarin red solution (dissolved in distilled water) for 10min at room temperature. The wells were rinsed five times with distilled water and photographed using phase-contrast microscopy. The alizarin red stain was eluted by incubation in 10% cetylpyridinium chloride monohydrate (dissolved in distilled water) for 30min, and the dye was quantified by absorption at OD540.7
The constructs were washed in PBS and fixed in 10% formalin for 1 day, decalcified with immunocal solution (Decal Chemical, Tallman, NY) for 1 day, dehydrated with graded ethanol washes, embedded in paraffin, sectioned to 5μm, and mounted on glass slides. The sections were deparaffinized with Citrisolv, rehydrated with a graded series of ethanol washes, and then stained for total collagen using Trichrome stainings. 4′-6-Diamidino-2-phenylindole staining was performed to observe nuclei.
The staining for bone sialoprotein (BSP) and osteopontin (OP) was carried out as follows: the rehydrated sections were blocked with normal serum, stained sequentially with primary antibodies (BSP: rabbit polyclonal anti-BSP II [AB1854; Chemicon, Temecula, CA], and OP: rabbit polyclonal anti-OP [AB1870; Chemicon]) and secondary antibody, and developed with a biotin/avidin system. The serum, secondary antibody, and developing reagents were obtained from Vector Laboratories (Burlington, CA) and included in the Vector Elite ABC kit (universal) (PK6200) and DAB/Ni Substrate (SK-4100). Negative controls were performed by omitting the primary antibody incubation step.
Samples were washed in PBS, fixed in 2% glutaraldehyde in sodium cacodylate buffer for 2h, washed in buffer, and freeze-dried overnight in a lyophillizer. Before imaging, samples were coated with gold/palladium. The inner and outer surfaces of the construct were imaged.
μCT was performed using a modified version of a previously established protocol.37 Samples were aligned along their axial direction and stabilized with wet gauze in a 15mL centrifuge tube. The tube was clamped in the specimen holder of a vivaCT 40 system (SCANCO Medical AG, Basserdorf, Switzerland). The 4mm length of the scaffold was scanned at 21μm isotropic resolution. The bone volume (BV) was obtained from the application of a global thresholding technique so that only the mineralized tissue is detected. The BV fraction was calculated as the fraction of measured BV per unit sample volume.
Data are presented as average±standard deviation. Statistical significance was determined using t-test and analysis of variance followed by Tukey's post hoc analysis, using STATISTICA software (StatSoft, Tulsa, OK). p<0.05 was considered significant.
Primary hASCs were characterized by fluorescence-activated cell sorting analysis to determine the presence of the following antigens: CD29 (98.9%), CD34 (92.3%), CD44 (24.3%), CD45 (12.1%), CD73 (79.0%), CD90 (94.9%), and CD105 (98.0%) (Fig. 1A). Quantitative biochemical assay showed significantly higher amounts of AP in osteogenic than in control cultures of hASCs (p<0.05) at all time points during cultivation (weeks 1–4) (Fig. 1B). Staining with alizarin red and von Kossa for mineral deposition corroborated this finding (Supplemental Fig. S1, available online at www.liebertonline.com).
The measurement of calcium levels in pellets of cells obtained from four different donors (A, B, C, and D) and cultured for 4 weeks in osteogenic or control medium showed that osteogenic culture conditions resulted in significantly higher (p<0.001) levels of calcium (Fig. 1C) and markedly stronger alizarin red staining (Supplemental Fig. S1). Strong mineral deposition after 4 weeks of culture under osteogenic conditions was confirmed by von Kossa staining of both monolayer cultures (Fig. 1E) and pellet cultures for all four donors tested (Fig. 1D, F, G, H). The control samples cultured in unsupplemented medium were negative (insets in Fig. 1D–H). Collectively, these data show strong effects of osteogenic supplements and time of culture, and a significant donor-to-donor variability in the osteogenesis of hASCs.
The efficiency of cell seeding, calculated as a fraction of the initial cells detected in the scaffold after seeding, was 73%±14%. Bioreactor cultivation enabled uniform flow of medium through six constructs simultaneously (Fig. 2A, B). Only viable cells were observed in all samples and at all time points throughout the 5 weeks of culture (Fig. 2C, where green stain indicates live cells in representative samples cultured for 5 weeks in perfusion or statically). This result was obtained for both construct culture groups and both media compositions (Supplemental Fig. S2, available online at www.liebertonline.com).
DNA assay demonstrated that cell proliferation occurred mostly during the first 2 weeks of cultivation (Fig. 2D). At the end of culture, cell numbers were significantly higher for samples cultured in osteogenic when compared with control medium (p<0.05), for all types of cell culture: monolayers (3.7-fold), pellets (2-fold), statically cultured constructs (1.5-fold), and constructs cultured with perfusion (2.5-fold) (Fig. 2E). Parallel differentiation studies of hMSCs derived from bone marrow aspirates showed the levels of differentiation markers comparable to those of hASCs (data not shown).
4′-6-Diamidino-2-phenylindole staining showed striking differences in cell distribution between constructs cultured statically compared with those cultured with medium perfusion. Homogenously seeded scaffolds (Fig. 3A) that were subsequently cultured statically in osteogenic medium for 5 weeks contained cells mostly within a thin peripheral region of the construct (Fig. 3B). In contrast, in the matching constructs cultured with perfusion, cells were distributed throughout the entire construct volume (Fig. 3C). The formation of collagen matrix was observed predominantly at the periphery of statically cultured constructs and throughout perfused constructs (Fig. 3E–F). Notably, the regions with high cell density (Fig. 3B, C) colocalized with the regions containing high amounts of new collagen matrix (Fig. 3E, F).
Constructs cultured in control medium in either static or perfused culture displayed no presence of either BSP (Fig. 4A, E) or bone OP. In osteogenic medium, collagen and OP were detected after 2 weeks of culture (data not shown). After 5 weeks of culture, statically cultured constructs showed deposition of BSP (Fig. 4B), OP (Fig. 4C), and collagen (Fig. 4D) in the outer but not inner regions of the constructs. In contrast, constructs cultured with perfusion exhibited uniform spatial distributions of all three proteins (Fig. 4F–H).
Mineralization of perfused constructs was monitored using μCT, to determine that the BV fraction increased by 8% after 5 weeks of cultivation with medium perfusion (Fig. 5A, B). Scanning electron microscopy images show that cells and deposited matrix filled out pore spaces in the outer (Fig. 5C, D) as well as in inner construct regions (Fig. 5E, F) and that small round crystals formed at construct surfaces (Fig. 5D).
In this study, we investigated the capacity of hASCs to form bone grafts when cultured on scaffolds made of decellularized bone, with perfusion of culture medium containing osteogenic supplements. Previously published studies documented the osteogenic potential of hASCs in static culture on a variety of scaffolds.10–14,38 However, little is known about the effects of perfusion (interstitial flow) on spatial distribution of these cells and the formation of bone during prolonged culture. We have previously shown that hMSCs derived from bone marrow aspirates could be induced to proliferate and form spatially uniform bone on decellularized bone scaffolds if cultured with medium perfusion.31 Although some studies suggested that hASCs may be less suitable for bone tissue engineering than hMSCs,39 our study suggested similar differentiation capabilities of hASCs and hMSCs for bone formation.5,31,40
The starting hASCs (passage 0) were characterized by flow cytometric analysis of surface antigens (Fig. 1A) to assess the initial levels of marker expression for various donors. In an earlier study that we conducted with hASCs, the expression patterns for mesenchymal cell markers (CD105, CD73, and CD90) stayed consistently high over several passages in monolayer culture.9 However, we also tested the expanded hASCs (passage 3) for osteogenic differentiation using biochemical assays and immunostains to further address the donor-to-donor variability and confirm the ability of passaged cells for osteogenic differentiation (Fig. 1C–H and Supplemental Fig. S1).
Decellularized bone scaffolds supported the attachment and proliferation of hASCs, in a manner similar to that shown previously for hMSCs31; however, hASC-based constructs yielded five times higher cellularity after 5 weeks of cultivation starting from the same initial seeding densities.
With respect to the presence of live cells only within the peripheral 200–300μm thick layer shown in previous studies,27 we observed live cells at millimeter depths in all culture groups (Fig. 3B, C, E, F). The outer construct regions contained a dense layer of cells, as in previous studies of alveolar osteoblasts,41 calvarial osteoblasts,27 and rat MSCs.42 Notably, the formation of an outer layer of cells can additionally contribute to insufficient nutrient–waste exchange in the construct interior. Further studies in our lab as well as reports in the literature43,44 indicate that hypoxia negatively affects osteogenic differentiation of hASCs. Thus, insufficient oxygenation in the central construct regions could correlate with the nonuniform differentiation of cells and result in nonuniform bone matrix deposition. In contrast, medium perfusion enabled the cultivation of large constructs with spatially uniform distributions of cells, consistent with our previous studies of hMSC-based bone constructs.31 Improved cell distribution in perfusion culture was also shown for other tissue engineering systems with medium perfusion.28–30 In general, uniform cell distribution is an important factor for uniform formation of the bone matrix.20,38
Cell densities observed in perfused constructs engineered in this study (~76 million cells/cm3 scaffold volume, based on DNA assay) are lower than those in native cancellous bone (~500 million cells/cm3).45 Nevertheless, these values are 3–10 times higher than cell densities in tissue-engineered bone grafts cultured under perfusion that have been reported thus far: 24 million cells/cm3,28 19 million cells/cm3,29 15 million cells/cm3,31 or 7 million cells/cm3.30
Interestingly, the presence of osteogenic supplements consistently resulted in higher proliferation of hASCs in all culture models (monolayer, pellet, static, and perfused constructs culture; Fig. 2E), which could be of importance in clinical applications where high cell numbers are needed. The same trend was observed in studies using hMSCs4 and rabbit ASCs46; however, it contrasts the findings with rat MSCs.47
Ascorbic acid, besides its role in collagen production,48 is a potent positive modulator of hMSC49 and hASC50 proliferation. In contrast, both increases51 and decreases47 in cell proliferation have been associated with the use of dexamethasone in culture medium. Decellularized bone scaffolds did not induce bone matrix deposition by hASCs in the absence of osteogenic supplements (Fig. 1A, E), consistent with nonosteoinductive properties of the scaffolds observed in vivo.52 It has also been suggested that partial matrix demineralization might be necessary for osteoinductive factors to become accessible to the cells.53 Further, the use of SDS in the process of decelullarization has been shown to affect the biochemical composition of native scaffolds (reduction of glycosaminoglycan content and collagen disruption) in anterior cruicate ligament54; therefore, it might have similar effects in bone matrix. Although bovine bone has been used as a scaffold in our study, human bone source could be considered for actual clinical applications. We are now working on the design of synthetic scaffolds mimicking the structure and mechanical properties of decellularized native bone, and this may be an attractive off the shelf alternative to the use of decellularized human bone.
hASC proliferation and osteogenesis was in agreement with the known sequence of in vitro osteoblast development and maturation.35 Collagen is the major organic component of the bone matrix and is secreted by osteoblasts during early osteoblastic differentiation before matrix calcification.55 Subsequently, cells stop proliferating and start to deposit OP and BSP, both being markers of the final-mineralization phase in osteoblast development.35 The presence of newly formed mineral in constructs additionally confirmed mature osteoblast-like characteristics of hASC constructs (Fig. 5B).
The regions with newly deposited bone matrix, rich in collagen, BSP, and OP, colocalized with regions of high cell density (Fig. 3), suggesting that high cell densities enhance bone matrix production, as during the normal developmental sequence, where mesenchymal condensation precedes ossification. Additional supporting evidence for the beneficial role of high cell density on osteogenic differentiation is the stronger mineralization (noted by von Kossa staining) of the cells in pellet cultures compared with monolayer cultures (Fig. 1D, E). In pellet cultures, close proximity of the cells and a three-dimensional environment contribute to osteogenic differentiation.
Perfused constructs displayed more uniform distributions of bone matrix than statically cultured constructs. Improved nutrient exchange and shear stress induced by medium flow have been shown to account for improved osteogenic phenotype in MSCs.28–31 In our system, medium flow alone, without osteogenic supplements, was not sufficient to induce osteogenic differentiation in hASCs. This might be due to the insufficient magnitude of shear stress, different nature of the stimulus (steady, unidirectional shear vs. oscillating flow), or the fact that ASCs need a certain extent of osteogenic predifferentiation before they can show response to shear stress.33 It should be noted that the shear stress values in our system were of the order of 0.01 Pa,31 whereas a mean shear stress of 0.6 Pa of pulsating fluid flow was reported to induce bone-like responsiveness for ASCs in two-dimensional parallel-plate flow chamber.33,34
In summary, perfusion culture of hASCs on decellularized bone scaffolds in the presence of osteogenic supplements resulted in millimeters thick, viable bone-like constructs, with strong expression of osteoblastic phenotype. Osteogenic supplements significantly increased construct cellularity, and the perfusion markedly improved the amounts and distributions of cells and bone matrix. Our model provides a starting point to engineer bone constructs for potential clinical use, as the hASCs are an easily accessible cell source, the decellularized bone scaffolds provide mechanical stability, and the bioreactor culture assures proper maturation of bone grafts. One of the main challenges is the survival of these highly cellular constructs after implantation; therefore, suitable ways of vascularization should be explored. hASC-based grafts can also serve as tools for bone disease or development studies.
The authors are grateful to Leo Q. Wan, Supansa Yodmuang, and Sarindr Bhumiratana for their help with experiments; Elizabeth Clubb and James Wade for providing liposuction aspirates; and Gang Yu and Xiying Wu for help with cell isolation and characterization. The work was supported in part by NIH (P41-EB002520 and R01-DE16525 to G.V.N., and P30 DK072476 to J.M.G.), the Pennington Biomedical Research Foundation (to J.M.G.), and the Ministry of Higher Education, Science, and Technology of Slovenia (3311-04-831828).
All authors have no conflict of interests.