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Article

Influence of Mesenchymal Stem Cell Sources on Their Regenerative Capacities on Different Surfaces

by
Arkaitz Mucientes
1,
Eva Herranz
1,
Enrique Moro
2,
Aranzazu González-Corchón
3,
María Jesús Peña-Soria
4,
Lydia Abasolo
1,
Luis Rodriguez-Rodriguez
1,
Jose Ramon Lamas
1,† and
Benjamín Fernández-Gutiérrez
1,*,†
1
UGC de Reumatología, Hospital Clínico San Carlos, IdISSC, 28040 Madrid, Spain
2
UGC de Traumatología, Hospital Clínico San Carlos, IdISSC, 28040 Madrid, Spain
3
Servicio de Cirugía Oral y Maxilofacial, Hospital Clínico San Carlos, IdISSC, 28040 Madrid, Spain
4
Servicio de Cirugía I, Hospital Clínico San Carlos, IdISSC, 28040 Madrid, Spain
*
Author to whom correspondence should be addressed.
†
Co-senior authors.
Cells 2021, 10(2), 481; https://0-doi-org.brum.beds.ac.uk/10.3390/cells10020481
Submission received: 15 January 2021 / Revised: 17 February 2021 / Accepted: 19 February 2021 / Published: 23 February 2021
(This article belongs to the Special Issue Oral Stem Cells in Tissue Engineering and Regenerative Medicine)
Browse Figures
Versions Notes

Abstract

:
Current gold-standard strategies for bone regeneration do not achieve the optimal recovery of bone biomechanical properties. To bypass these limitations, tissue engineering techniques based on hybrid materials made up of osteoprogenitor cells—such as mesenchymal stem cells (MSCs)—and bioactive ceramic scaffolds—such as calcium phosphate-based (CaPs) bioceramics—seem promising. The biological properties of MSCs are influenced by the tissue source. This study aims to define the optimal MSC source and construct (i.e., the MSC–CaP combination) for clinical application in bone regeneration. A previous iTRAQ analysis generated the hypothesis that anatomical proximity to bone has a direct effect on MSC phenotype. MSCs were isolated from adipose tissue, bone marrow, and dental pulp, then cultured both on a plastic surface and on CaPs (hydroxyapatite and β-tricalcium phosphate), to compare their biological features. On plastic, MSCs isolated from dental pulp (DPSCs) presented the highest proliferation capacity and the greatest osteogenic potential. On both CaPs, DPSCs demonstrated the greatest capacity to colonise the bioceramics. Furthermore, the results demonstrated a trend that DPSCs had the most robust increase in ALP activity. Regarding CaPs, β-tricalcium phosphate obtained the best viability results, while hydroxyapatite had the highest ALP activity values. Therefore, we propose DPSCs as suitable MSCs for cell-based bone regeneration strategies.

1. Introduction

Bone regeneration and bone remodelling can be considered two sides of the same coin. While bone remodelling is a life-long process, bone regeneration occurs mainly during bone healing [1]. It is described that, for small fractures or injuries, the bone has an innate ability to repair without scarring [2]. These regenerative processes are largely surpassed by major bone damage, such as skeletal reconstruction surgeries, bone defects of various origins (e.g., traumatic, infectious, or tumoral), or congenital skeletal dysplasias. Current orthopaedic surgery strategies are mostly bone grafting (both autologous and allogeneic) and osteodistraction [3]. They can be combined with the use of growth factors or osteoinductive scaffolds. However, the successful recovery of the biomechanical properties of bone is limited. To bypass these limitations, novel strategies have been developed. Among these, hybrid materials consisting of osteoprogenitor cells, such mesenchymal stem cells (MSCs) and bioactive ceramic scaffolds, have been proposed as promising tools [4].
Calcium phosphate-based (CaPs) bioceramics have been used both in maxillo-facial surgeries and dentistry for over 30 years. CaPs are biocompatible, osteoconductive, osteoinductive and, in some cases, bioactive. Due to these properties, CaPs have been widely used as scaffolds for bone regeneration and tissue engineering. Among the different CaPs bioceramics, hydroxyapatite (HA) and β-tricalcium phosphate (β-TCP) have been widely used [5]. The Ca:P ratio determines certain properties, such as solubility and tendency for resorption in the body [6]. HA is considered relatively non-biodegradable, while β-TCP degrades readily and can be completely replaced by newly formed bone.
Adult MSCs can be isolated from almost every tissue [7]. They have multipotential capacities and can differentiate into cells of several mesenchymal lineages (e.g., cartilage, bone, tendons, muscles, and adipocytes), among other cell types [8]. Moreover, MSCs have migratory and homing abilities that are crucial for wound healing, and their immunomodulatory and immunological tolerance induction potentials have been communicated [9,10,11]. Although MSCs derived from different sources present similar phenotypic characteristics, the intensity of these varies depends on the tissue source [12].
Bone marrow MSCs (BM-MSCs) were the first MSCs known, described by Friedenstein et al. [13]. They have been widely used and studied in trials looking for potential regenerative therapies. Adipose-derived MSCs (ASCs) present several advantages, compared to MSCs obtained from other sources: Adipose depots are ubiquitous in the body, easily accessible with minimal invasion, and contain a large number of stem cells [14]. Furthermore, their capacity to promote osteogenesis in animal models has been described [15]. MSCs isolated from dental pulp (DPSCs) are usually isolated after the surgical removal of wisdom teeth and, so, they are considered a non-invasive source of MSCs. DPSCs present a high proliferative capacity and easily differentiate into odontoblasts, osteoblasts, and chondrocytes [16,17]. DPSCs have been recently proposed for use in regenerative therapies for bone diseases, among other conditions [18].
Considering the osteogenic potential as a property influenced by the tissue, several comparative studies of MSCs derived from various sources on different surfaces have been published [19,20,21,22,23,24]. Despite these studies, clarification is still needed regarding the influence of the cell source and surface on the osteogenic potential. Osteogenic potential maximisation in the context of bone-regeneration processes would serve as an important step. This study aims to define the MSC source and construct (MSC and scaffold) combination with the highest osteogenic potential.

2. Materials and Methods

2.1. Proteomic Analysis by iTRAQ Labelling

Data were obtained in a previous proteomic analysis, in which MSCs from subchondral bone and cartilage were compared (not published). Specifically, the results obtained after comparing these locations in healthy individuals were analysed.
Briefly, MSCs were obtained surgically from subchondral bone and cartilage of a donor without osteoporotic or osteoarthritic signs. Total protein content was isolated, dried in air, and then re-suspended in 25 μL of iTRAQ dissolution buffer (ABSciex, Foster City, CA, USA). Protein concentrations were determined by Bradford assay (Sigma-Aldrich, St. Louis, MO, USA). TRAQ labelling (ABSciex, Foster City, CA, USA) was performed with SB(116) and C(117) mass tags and desalted with home-made C-18 Stage-tips. Fractions separated in a nanoLC system (Tempo, Eksigent) were automatically deposited on a MALDI plate and analysed by MS/MS (4800 MALDI-TOF/TOF system; ABSciex). Relative quantitative analysis was performed using the ProteinPilot software (ABSciex) with the Paragon™ Algorithm for protein identification and quantification. Only proteins identified with at least 95% confidence, a Prot Score of at least 1.3, a p-value ≤ 0.05, and ratio ≠ 1 were considered as modulated.

2.2. Samples

MSCs from three different localisations (bone marrow, dental pulp, and adipose tissue), obtained from healthy donors (Table 1), were used for in vitro biological studies. Written informed consent was obtained from all donors before sample collection. The study was approved following the guidelines of the institutional ethics committee (Comité Ético de Investigación Clínica Hospital Clínico San Carlos) and the principles expressed in the Declaration of Helsinki.
Discs of CaPs bioceramics used in this study were synthesised, sintered, and polished (if needed). They were kindly supplied by the Instituto de Cerámica y Vidrio (ICV-CSIC). The discs had a diameter of 18 mm and 4 mm thickness. The sintering temperature employed for β-TCP was 1130 °C, and that for HA was 1250 °C [25,26].

2.3. Cell Isolation and Culture

ASCs were obtained from adipose tissue after surgical biopsies, according to Yang et al. [27]. DPSCs were isolated after dental pulp mechanical extraction from wisdom exodontias, as described by Huang et al. [28]. Finally, BM-MSCs were obtained from femoral channel aspirates of bone marrow, taken during joint replacement surgery, in a Ficoll density gradient and cultured directly, as described by Gudlevicine et al. [29].
Once isolated, cells were expanded in growth medium: DMEM supplemented with 10% FBS and antibiotics. DPSCs required 20% FBS, instead of the 10% usually established, as described by Alkhalil et al. [30]. Cell cultures were expanded at 37 °C in a 5% CO2 atmosphere. The medium was changed every 3 days until cell confluence at passage 3.

2.4. Cell Characterisation

In order to confirm that cells satisfied the minimal criteria for the definition of MSC proposed by the International Society for Cellular Therapy [31], flow cytometry and histochemistry assays were carried out, as we have previously described [32].

2.5. Biological Features on the Plastic Surface

2.5.1. MSC Proliferation Rate

During cell expansion, cell proliferation was evaluated by calculating the population doubling time (Dt), which is defined by:
Dt = T ln2/ln(Nf/Ni)
where “T” represents the time elapsed between determinations of the final number of cells (Nf) obtained from an initial cell number (Ni).

2.5.2. Osteogenic Commitment of Each MSC

Alizarin Red staining was carried out along culture on plastic. The coloured area of cell cultures after Alizarin red staining was quantified, in terms of percentage, using the ImageJ 1.43v software (National Institutes of Health, freely available: https://imagej.nih.gov/ij/index.html, accessed on 5 November 2020).

2.6. Cell Behaviour on CaPs

2.6.1. Cell Activity/Viability

Prior to cell seeding, the scaffolds were previously submerged in growth medium for 24 h, then seeded with 1 mL of a cellular suspension containing 50,000 cells.
Monitoring of cell viability was conducted using the colourimetric indicator AlamarBlue™ (Cat#Y00-100. Thermo Fisher Scientific, Waltham, MA USA). The variation of absorbance at 570 nm was measured at 24 h, 4 days, and 7 days using a Heales MB-580 microplate reader (Shenzhen Heales Technology Development Co. Ltd., Shenzhen, China). The amount of absorbance corresponded to cell metabolic activity.

2.6.2. Scanning Electronic Microscopy (SEM)

The cellular organisation, adhesion, and colonisation of the scaffolds were assessed at 24 h and 7 days. Each sample was subjected to fixation with phosphate buffer solution containing 4% paraformaldehyde and 2.5% glutaraldehyde for 30 min. After fixation, samples were washed 3 times with phosphate-buffered saline (PBS) for 20 min, followed by incubation for 45 min with a solution of 1% osmium tetraoxide and, finally, washed again with PBS 3 times for 10 min. The next step was the dehydration of samples by immersing them in increasing ethanol concentrations: 30%, 50%, 70%, 96%, and 100%. The final step was to introduce the samples into a critical-point device and cover them with vaporised gold. Samples were then observed and analysed by scanning electron microscopy (SEM JEM 6400, JEOL, Akishima-shi, Japan).

2.6.3. ALP Activity

Early osteoblast differentiation was evaluated by measuring the alkaline phosphatase (ALP) activity, which is expressed just before the matrix mineralisation occurs, and its role as an osteogenic activity marker is established [33]. The evaluation was made using 24-well plates, and three conditions for each sample were evaluated: cell in plastic with growth medium as an internal control, and cells seeded on HA with osteogenic medium or β-TCP with osteogenic medium. Duplicates for each experimental condition were made.
Osteogenesis progression was measured between 24 h and 7 days. At these time points, media were discarded, and ceramic discs recovered, washed with PBS, stored at −20 °C, and soaked in lysis buffer (0.1 wt%, Triton-X 100, 1 mM MgCl2, 0.1 mM ZnCl2). ALP activity was determined by a colourimetric method using a commercial kit (Thermo Fisher Scientific, Cat#37629), following the manufacturer instructions, and measuring the absorbance at 405 nm.

2.7. Statistical Analysis

Statistical analysis was performed using the GraphPad Prism version 7.00 software for Windows (GraphPad Software, La Jolla, CA, USA; www.graphpad.com, accessed on 5 November 2020). We used one-way ANOVA followed by Bonferroni post-hoc tests and two-tailed paired/unpaired Student t-tests for comparison of normal variables. The level of significance p < 0.05 was considered statistically significant. Each experiment was performed with replicates.

3. Results

3.1. iTRAQ Results Analysis

The difference in protein components between MSCs from subchondral bone and cartilage were analysed using an iTRAQ-based comparative analysis. The results obtained revealed the identification of 1012 unique proteins in the samples. Fifty of these proteins displayed statistically significant differences (Table 2). Among those, five proteins have been previously associated with the osteoblast differentiation process: PALLD, HSPA5/GRP78, FLNA, IGFBP3, and DSTN.

3.2. Biological Features on the Plastic Surface

The proliferation rate and osteogenic potential of MSCs when cultured on plastic surfaces were measured (Figure 1).
Figure 1A shows the proliferation rate results. BM-MSCs and ASCs showed identical doubling time, while DPSCs proliferated more rapidly (ASCs = 10 days, BM-MSCs = 10 days, DPSCs = 1.76 days, pANOVA < 0.0001, pDPSC-ASC = 0.0003, pDPSC-BM-MSC = 0.0003, pASC-BM-MSC > 0.9999).
Furthermore, Alizarin Red staining showed that DPSCs presented a much more extended stained area than the other sources (Figure 1B), where its quantification ratified the significant differences among MSCs (ASCs = 9.4210%, BM-MSCs = 39.7150%, DPSCs = 72.5965%; pANOVA = 0.0038, pDPSC-ASC = 0.0063, pDPSC-BM-MSC = 0.0250, pASC-BM-MSC = 0.0473).

3.3. Cell Behaviour on CaPs

3.3.1. Viability Test

Figure 2A shows that cells on β-TCP had higher viability values than cells on HA (t = 24 h, β-TCP = 0.0500, HA = 0.0568, p = 0.0246; t = 4 days, β-TCP = 0.0872, HA = 0.0459, p ˂ 0.0001; t = 7 days, β-TCP = 0.1144, HA = 0.0690, p = 0.0021).
Figure 2B shows that the viability test results were not different, regarding the cell source at day 7 (t = 7 days, ASCs = 0.0748, BM-MSCs = 0.1131, DPSCs = 0.1029, pANOVA = 0.2141, pDPSC-ASC > 0.9999, pDPSC-BM-MSC = 0.0206, pASC-BM-MSC = 0.2584), but there were significant differences favouring DPSCs at 24 h and at 4 days (t = 24 h, ASCs = 0.0323, BM-MSCs = 0.0363, DPSCs = 0.0699, pANOVA ˂ 0.0001, pDPSC-ASC < 0.0001, pDPSC-BM-MSC = 0.0003, pASC-BM-MSC > 0.9999; t = 4 days, ASCs = 0.0627, BM-MSCs = 0.0831, DPSCs = 0.0708, pANOVA = 0.0249, pDPSC-ASC > 0.9999, pDPSC-BM-MSC = 0.7430, pASC-BM-MSC = 0.2460). When analysing the viability of each construct (Figure 2C), BM-MSCs showed significant higher values seeded on β-TCP while ASCs and DPSCs did not (t = 24 h, ASCs + HA = 0.0285, ASCs + β-TCP = 0.05375, BM-MSCs + HA = 0.0346, BM-MSCs + β-TCP = 0.01267, DPSCs + HA = 0.0318, DPSCs + β-TCP = 0.02171, pANOVA = 0.0002; t = 4 days, ASCs + HA = 0.0454, ASCs + β-TCP = 0.0658, BM-MSCs + HA = 0.0350, BM-MSCs + β-TCP = 0.0908, DPSCs + HA = 0.0404, DPSCs + β-TCP = 0.0348, pANOVA < 0.0001; t = 7 days, ASCs + HA = 0.0517, ASCs + β-TCP = 0.0638, BM-MSCs + HA = 0.0537, BM-MSCs + β-TCP = 0.1222, DPSCs + HA = 0.0422, DPSCs + β-TCP = 0.0765, pANOVA = < 0.0001).

3.3.2. Scanning Electronic Microscopy

Cell morphology and behaviour, when grown on β-TCP and HA scaffolds, were studied by SEM at both 24 h and 7 days after culture. In all cases, cells did not show visual signs of cytotoxicity. Cells were visualised in their normal shape and size.
Regarding β-TCP, cell adhesion seemed to be faster in BM-MSCs (Figure 3C) than in ASCs and DPSCs (Figure 3A,E, respectively). After 7 days, cell overlays were observed in β-TCP discs, independently of the MSC seeded (Figure 3B,D,F). When culturing on HA, the adhesion process was similar for all MSCs (Figure 4A,C,E). On day 7, BM-MSCs and ASCs (Figure 4B–D) exhibited similar appearances, where the number of cells increased without forming layers. In contrast, DPSCs (Figure 4F) formed a multilayer covering the entire surface. Finally, all MSCs colonised the existing internal pores in both CaPs (Figure 5).

3.3.3. Osteogenic Potential

Figure 6A shows a significant differential ALP activity at both 24 h and 7 days, which was higher on HA (t = 24 h, β-TCP = 0.4249, HA = 0.6213, p = 0.0014; t = 7 days, β-TCP = 0.6201, HA = 0.9517, p = 0.0002).
According to cell localisation (Figure 6B), each localisation showed a significant increase in ALP activity (ASCs, t1 = 0.515, t2 = 0.9060, p = 0.0007; BM-MSCs, t1 = 0.6293, t2 = 0.8686, p = 0.0358; DPSCs, t1 = 0.417, t2 = 0.7147, p = 0.0002). The initial differences between locations disappeared at the final time point (t = 24 h, ASCs = 0.5150, BM-MSCs = 0.6293, DPSCs = 0.4170, pANOVA = 0.0306, pDPSC-ASC = 0.2790, pDPSC-BM-MSC = 0.0277, pASC-BM-MSC > 0.9999; t = 7 days, ASCs = 0.9016, BM-MSCs = 0.8636, DPSCs = 0.7147, pANOVA = 0.2394, pDPSC-ASC = 0.3416, pDPSC-BM-MSC = 0.5712, pASC-BM-MSC > 0.9999).
Finally, the increase in ALP activity (in percentage) was calculated. DPSCs presented a bigger, although not significant, increase in ALP activity than the other sources (ASCs = 62.58%, BM-MSCs = 40.15%, DPSCs = 72.51%, pANOVA = 0.1479, pDPSC-ASC > 0.9999, pDPSC-BM-MSC = 0.1969, pASC-BM-MSC = 0.4091; Figure 6C). Regarding biomaterial–cell combinations, DPSC + HA increased the most, although no significant differences were obtained (ASCs + HA = 98.60%, BM-MSCs + HA = 43.46%, DPSCs + HA = 132.20%, ASCs + β-TCP = 78.38%, BM-MSCs + β-TCP = 112.20%, DPSCs + β-TCP = 56.44%, pANOVA = 0.2425; Figure 6D).

4. Discussion

In the bone regeneration context, therapies based on the use of osteoprogenitor cells have shown promise. However, the full therapeutic potential of these techniques has not yet been achieved. A full understanding of how different biological aspects influence the osteogenic potential is required. The anatomical localisation of the cells used is among those characteristics. To our knowledge, this is the first comparative work that has analysed a possible osteogenic commitment depending on the anatomic localisation of non-commercial human MSCs from bone marrow, adipose tissue, and dental pulp seeded both on a plastic surface and CaPs (β-TCP and HA).
The starting point of this work was the analysis of the results obtained in a previous iTRAQ analysis, where MSCs from subchondral bone and cartilage were compared in an osteoarthritis (OA) study. OA is a condition characterised by excessive bone growth, with the main affected tissues being subchondral bone and cartilage. Specifically, the results obtained after comparing these locations in healthy individuals were analysed in a free-hypothesis context. Fifty proteins were identified (Table 2). Five of those 50 proteins have been communicated as being related to the osteogenic process. FLNA, HSPA5/GRP78, and PALLD were up-regulated in subchondral bone, and their expression has been correlated with osteoblast differentiation, as they contribute to the stabilisation of cytoskeleton, which is necessary for the osteogenesis and regulation of protein folding and calcium flux [34,35,36,37]. In contrast, DSTN and IBP3—inhibitors of osteoblast differentiation [38,39]—were down-regulated in MSCs isolated from the subchondral bone. Considering this background, MScs from subchondral bone display a more established commitment to osteogenesis, compared to MSCs from cartilage. This supports the hypothesis that anatomical proximity to bone has a direct effect on MSC phenotype, in terms of increased osteogenic commitment. Further studies are required to clarify whether this commitment is due to cell location or cell inherent properties.
To confirm this hypothesis, we analysed the biological behaviour of MSCs isolated from locations with different proximity to bone (adipose tissue, bone marrow, and dental pulp) on different surfaces. All cells used in this work met the minimal criteria to be defined as MSCs (Figure A1) [31].
On plastic surfaces, proliferative ability and osteogenic potential were studied. Evaluating cell proliferation is important for cell-based therapies, as it has been communicated that stem cell therapy failures are likely to be due to a massive cell death occurring after cell transplantation [40]. Our results established that DPSCs have the highest proliferation rate (Figure 1A), in line with previous studies [19,24]. Furthermore, it was observed that DPSCs presented a smaller size. As DPSCs have a higher proliferation rate, this smaller size is likely a consequence, due to the indirect relationship between proliferation and cell size [41]. Alizarin Red staining is commonly used as an osteogenic differentiation indicator, as mineralized nodules are red-coloured. Microscopy images show that DPSCs exhibited the most intense staining, with its quantification evidencing significant differences (Figure 1B). These results indicate that DPSCs presented the most osteogenic capacity in vitro, followed by BM-MSCs and ASCs as the least osteogenic. This staining pattern confirms and extends the results obtained by Tamaki et al. [19]. Furthermore, it has been described that DPSCs likely have an advantage for osteogenic differentiation over other MSCs [22], as DPSCs only differentiate into osteoblasts at high passages [42].
Once the constructs were generated, we studied their cell viability, colonisation ability, and osteogenic capacity. The viability test showed that β-TCP was more cell-friendly than HA (Figure 2A,C). Both β-TCP and HA are biomaterials commonly used in bone tissue engineering and dentistry to treat bone defects. Implant surface quality is a major factor in biocompatibility. When the surface of the implanted biomaterial is exposed to tissue fluids, an initial interaction occurs between the living bone and tissue and the implant surface. In this sense, the use of materials filled with tricalcium phosphate appears promising, following the observation that more living cells are in this material [43]. Regarding MSCs, the viability test was favourable for DPSCs at 24 h and 4 days, compared to ASCs or BM-MSCs; however, these differences were not significant at 7 days (Figure 2B).
SEM images (Figure 3 and Figure 4) were coherent, as only DPSCs developed a cell layer on HA; whereas, on β-TCP, all three source-derived MSCs achieved this. CaPs are porous, so pore colonisation by the cells is required for the optimal colonisation of the CaP. Specific images of the pores existing in both CaPs prove the pores were successfully colonised by all MSCs after 24 h (Figure 5). Furthermore, cytotoxicity was not observed in the studied samples. Remarkably, DPSCs showed the greatest proliferation ability on both plastic and bioceramic surfaces. This feature provides an advantage for bone regeneration, as high MSCs density enhances osteogenic differentiation [44]. These results, together with those on plastic surfaces and previous studies, highlight the features of DPSCs for dental and bone regeneration applications [21,45].
The interplay of the tissue engineering triad (cells, signalling molecules, and scaffolds) is essential for recapitulation of the biological events of tissue regeneration. These elements have been used, either separately or in combination, for the reconstitution of the pulp–dentin complex and bone defects. In the literature, it is established that the mechanical properties of the scaffold influence cell processes such as proliferation and differentiation [46]. Recent data have implied that β-TCP is a bioactive and biocompatible material, capable of enhancing the proliferation, migration, and adhesion of DPSCs. Moreover, recent data have been conclusive about the higher levels of osteogenic and odontogenic differentiation markers related to DPSCs, such as COLI, DSPP, OC, RUNX2, and DMP-1. Our results suggest, in accordance with the literature, that DPSCs may be a valuable tool in the context of dental and bone regeneration [47].
Regarding osteogenic potential, the ALP activity test results (Figure 6A) mismatched with the viability results (Figure 2A): while β-TCP appeared to be the best in terms of viability, HA obtained the highest values in ALP activity. These results indicate that a combination of materials may be more effective. Referring to cell sources, ASCs and BM-MSCs presented similar absolute values, which were slightly superior to that of DPSCs, but not significant (Figure 6B). Interestingly, this pattern in ALP activity was obtained in recent studies comparing multisource-derived MSCs seeded on plastic surfaces, although authors communicated significant differences [23,24]. The absence of significance in our results could be due to the osteoinductive properties that both CaPs present, which the plastic surface lacked [48,49]. As DPSCs presented the highest metabolic activity during osteogenesis on both CaPs (Figure A2), we consider it conceivable that CaPs can enhance osteogenesis preferentially in DPSCs over other MSCs.

5. Conclusions

Our results indicate DPSCs as the ideal cell for bone regeneration scenarios. Within bone regeneration, DPSCs are potentially beneficial in periodontal regeneration. Supporting this, a Phase 3 clinical study using DPSCs for alveolar cleft lip and palate repair has recently been initiated (ClinicalTrials.gov Identifier: NCT03766217), and promising results regarding the use of DPSCs for periodontal regeneration have been published [50]. Moreover, a combination of the best viability obtained with β-TCP and the enhanced osteogenic capacity of HA may be appropriate. Future studies are necessary to obtain the best combination of cells and biomaterials, together with other signalling enhancers or inhibitors and different proteins that have been demonstrated in the field of dentistry and bone regeneration [51].

Author Contributions

Conceptualisation, J.R.L. and B.F.-G.; methodology, A.M. and E.H.; validation, A.M.; investigation, A.M. and E.H.; resources, E.M., A.G.-C., and M.J.P.-S.; data curation, A.M., J.R.L., L.A., and L.R.-R.; writing—original draft preparation, A.M.; writing—review and editing, J.R.L. and B.F.-G.; supervision, J.R.L.; funding acquisition, B.F.-G. All authors have read and agreed to the published version of the manuscript.

Funding

This work was supported by grants RIER (Instituto de Salud Carlos III) and FIS PI13/01863 (Instituto de Salud Carlos III).

Institutional Review Board Statement

The study was conducted according to the guidelines of the Declaration of Helsinki, and approved by the Institutional Review Board of Comité Ético de Investigación Clínica Hospital Clínico San Carlos.

Informed Consent Statement

Informed consent was obtained from all subjects involved in the study.

Data Availability Statement

The study reports no data.

Acknowledgments

We thank Pilar Pena and Carmen Baudín from the Instituto de Cerámica y Vidrio, (ICV-CSIC) for providing the bioceramic samples used in the study.

Conflicts of Interest

The authors declare no conflict of interest.

Appendix A

Cells 10 00481 g0a1 550
Figure A1. Characterisation of MSCs: (A) lineage-specific staining to confirm the correct differentiation into osteogenic, chondrogenic, and adipogenic lineages. Microscopy images show that all MSCs present the ability to differentiate into the 3 lineages; (B) flow cytometry results after analysing the surface marker profile of each MSC.
Figure A1. Characterisation of MSCs: (A) lineage-specific staining to confirm the correct differentiation into osteogenic, chondrogenic, and adipogenic lineages. Microscopy images show that all MSCs present the ability to differentiate into the 3 lineages; (B) flow cytometry results after analysing the surface marker profile of each MSC.
Cells 10 00481 g0a1
Cells 10 00481 g0a2 550
Figure A2. Cell activity during induced osteogenesis. Alamar Blue test results obtained by MSC–CaP combinations in osteogenic medium at the following time points: 24 h, 4 days, and 7 days. Data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01, *** p ≤ 0.001, **** p ≤ 0.0001.
Figure A2. Cell activity during induced osteogenesis. Alamar Blue test results obtained by MSC–CaP combinations in osteogenic medium at the following time points: 24 h, 4 days, and 7 days. Data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01, *** p ≤ 0.001, **** p ≤ 0.0001.
Cells 10 00481 g0a2

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Figure 1. Biological features of MSCs on the plastic surface: (A) MSC proliferation. Doubling time (in days) when cultured in plastic presented by MSC isolated from adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); and (B) Alizarin Red staining and its quantification of different source-derived mesenchymal stem cells—(1) Alizarin Red staining of ASCs after 21 days of culture in osteogenic medium (×10); (2) Alizarin Red staining of BM-MSCs after 21 days of culture in osteogenic medium (×10); (3) Alizarin Red staining of DPSCs after 21 days of culture in osteogenic medium (×10); and (4) Alizarin Red staining quantification of MSC, according to the cell source, adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs). All data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01 *** p ≤ 0.001.
Figure 1. Biological features of MSCs on the plastic surface: (A) MSC proliferation. Doubling time (in days) when cultured in plastic presented by MSC isolated from adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); and (B) Alizarin Red staining and its quantification of different source-derived mesenchymal stem cells—(1) Alizarin Red staining of ASCs after 21 days of culture in osteogenic medium (×10); (2) Alizarin Red staining of BM-MSCs after 21 days of culture in osteogenic medium (×10); (3) Alizarin Red staining of DPSCs after 21 days of culture in osteogenic medium (×10); and (4) Alizarin Red staining quantification of MSC, according to the cell source, adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs). All data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01 *** p ≤ 0.001.
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Figure 2. Cell viability, in terms of optical density at 570 nm, when seeded on CaPs: (A) average viability shown by all MSCs on each CaP—Hydroxyapatite (HA) and ß-tricalcium phosphate (β-TCP); (B) average viability shown by each MSC on both CaPs—Adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); (C) average viability shown by each construct. All data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01, *** p ≤ 0.001, **** p ≤ 0.0001.
Figure 2. Cell viability, in terms of optical density at 570 nm, when seeded on CaPs: (A) average viability shown by all MSCs on each CaP—Hydroxyapatite (HA) and ß-tricalcium phosphate (β-TCP); (B) average viability shown by each MSC on both CaPs—Adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); (C) average viability shown by each construct. All data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01, *** p ≤ 0.001, **** p ≤ 0.0001.
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Figure 3. The behaviour of MSCs seeded on ß-TCP scaffold at different time points: (A) ASCs on ß-TCP scaffold after 24 h (scale bar: 200 μm); (B) ASCs forming cell layer on ß-TCP scaffold after 7 days (scale bar: 200 μm); (C) BM-MSCs on ß-TCP scaffold after 24 h (scale bar: 200 μm); (D) BM-MSCs forming cell layer on ß-TCP scaffold after 7 days (scale bar: 200 μm); (E) DPSCs on ß-TCP scaffold at 24 h (scale bar: 50 μm); and (F) DPSCs forming cell layer on ß-TCP scaffold after 7 days (scale bar: 200 μm). Black arrows indicate unique cells. Green arrows indicate cell layers.
Figure 3. The behaviour of MSCs seeded on ß-TCP scaffold at different time points: (A) ASCs on ß-TCP scaffold after 24 h (scale bar: 200 μm); (B) ASCs forming cell layer on ß-TCP scaffold after 7 days (scale bar: 200 μm); (C) BM-MSCs on ß-TCP scaffold after 24 h (scale bar: 200 μm); (D) BM-MSCs forming cell layer on ß-TCP scaffold after 7 days (scale bar: 200 μm); (E) DPSCs on ß-TCP scaffold at 24 h (scale bar: 50 μm); and (F) DPSCs forming cell layer on ß-TCP scaffold after 7 days (scale bar: 200 μm). Black arrows indicate unique cells. Green arrows indicate cell layers.
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Figure 4. The behaviour of MSCs seeded on HA scaffold at different time points: (A) ASCs on HA scaffold after 24 h (scale bar: 100 μm); (B) ASCs forming cell layer on HA scaffold after 7 days (scale bar: 100 μm); (C) BM-MSCs on HA scaffold after 24 h (scale bar: 200 μm); (D) BM-MSCs forming cell layer on HA scaffold after 7 days (scale bar: 200 μm); (E) DPSCs on HA scaffold at 24 h (scale bar: 100 μm); and (F) DPSCs forming cell layer on HA scaffold after 7 days (scale bar: 1 mm). Black arrows indicate unique cells. Green arrows indicate cell layers.
Figure 4. The behaviour of MSCs seeded on HA scaffold at different time points: (A) ASCs on HA scaffold after 24 h (scale bar: 100 μm); (B) ASCs forming cell layer on HA scaffold after 7 days (scale bar: 100 μm); (C) BM-MSCs on HA scaffold after 24 h (scale bar: 200 μm); (D) BM-MSCs forming cell layer on HA scaffold after 7 days (scale bar: 200 μm); (E) DPSCs on HA scaffold at 24 h (scale bar: 100 μm); and (F) DPSCs forming cell layer on HA scaffold after 7 days (scale bar: 1 mm). Black arrows indicate unique cells. Green arrows indicate cell layers.
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Figure 5. MSCs colonising pores of both HA and ß-TCP scaffolds after 24 h: (A) existing pores in HA colonised by DPSCs (scale bar: 5 μm); (B) existing pores in HA colonised by BM-MSCs (scale bar: 300 μm); (C) existing pores in HA colonised by ASCs (scale bar: 10 μm); (D) existing pores in ß-TCP colonised by DPSCs (scale bar: 50 μm); (E) existing pores in ß-TCP colonised by BM-MSCs (scale bar: 10μm); and (F) existing pores in ß-TCP colonised by ASCs (scale bar: 200 μm). Black arrows indicate unique cells.
Figure 5. MSCs colonising pores of both HA and ß-TCP scaffolds after 24 h: (A) existing pores in HA colonised by DPSCs (scale bar: 5 μm); (B) existing pores in HA colonised by BM-MSCs (scale bar: 300 μm); (C) existing pores in HA colonised by ASCs (scale bar: 10 μm); (D) existing pores in ß-TCP colonised by DPSCs (scale bar: 50 μm); (E) existing pores in ß-TCP colonised by BM-MSCs (scale bar: 10μm); and (F) existing pores in ß-TCP colonised by ASCs (scale bar: 200 μm). Black arrows indicate unique cells.
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Figure 6. (A) Average ALP activity shown by all MSCs on each CaP—Hydroxyapatite (HA) and ß-tricalcium phosphate (β-TCP); (B) everage ALP activity shown by each MSC on both CaPs—Adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); (C) the average increase in ALP activity (in percentage) presented by each MSC on both CaPs—Adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); and (D) increase in ALP activity (in percentage) presented by each construct—Hydroxyapatite (HA), ß-tricalcium phosphate (β-TCP), adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs). All data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01, *** p ≤ 0.001.
Figure 6. (A) Average ALP activity shown by all MSCs on each CaP—Hydroxyapatite (HA) and ß-tricalcium phosphate (β-TCP); (B) everage ALP activity shown by each MSC on both CaPs—Adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); (C) the average increase in ALP activity (in percentage) presented by each MSC on both CaPs—Adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs); and (D) increase in ALP activity (in percentage) presented by each construct—Hydroxyapatite (HA), ß-tricalcium phosphate (β-TCP), adipose tissue (ASCs), dental pulp (DPSCs), and bone marrow (BM-MSCs). All data are shown as mean ± standard deviation. Significance level: * p ≤ 0.05, ** p ≤ 0.01, *** p ≤ 0.001.
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Table
Table 1. Main characteristics of healthy donors.
Table 1. Main characteristics of healthy donors.
DonorCell TypeSexAge
Donor 1BM-MSCF57
Donor 2BM-MSCM56
Donor 3BM-MSCM55
Donor 4ASCF53
Donor 5ASCF56
Donor 6ASCM50
Donor 7DPSCF44
Donor 8DPSCM58
Donor 9DPSCM59
BM-MSC: Bone marrow mesenchymal stem cell; ASC: Adipose-derived mesenchymal stem cell; DPSC: Dental pulp mesenchymal stem cell.
Table
Table 2. Differentially expressed proteins identified in MSC isolated from subchondral bone, compared to that from cartilage.
Table 2. Differentially expressed proteins identified in MSC isolated from subchondral bone, compared to that from cartilage.
Uniprot IDGeneProteinPeptidesFold Changep-Value
AMPN_HUMANANPEPAminopeptidase N2711.270.0001
PALLD_HUMANPALLDPalladin44.69890.0145
K2C1_HUMANKRT1Keratin, type II cytoskeletal 1114.63520.0164
TPM1_HUMANTPM1Tropomyosin alpha-1 chain134.36520.0173
TAGL_HUMANTAGLNTransgelin134.28550.0001
K1C10_HUMANKRT10Keratin, type I cytoskeletal 1083.56450.0085
FRIH_HUMANFTH1Ferritin heavy chain33.43560.034
DHB4_HUMANHSD17B4Peroxisomal multifunctional enzyme type 253.40410.0078
VIME_HUMANVIMVimentin2353.34200.0291
SQRD_HUMANSQRDLSulphide:quinone oxidoreductase, mitochondrial102.99230.0030
PDIA1_HUMANP4HBProtein disulphide-isomerase482.72900.0028
KPYM_HUMANPKM2Pyruvate kinase isozymes M1/M2692.60620.0123
ATPB_HUMANATP5BATP synthase subunit beta, mitochondrial212.53510.0118
GRP78_HUMANHSPA578 kDa glucose-regulated protein532.51190.0001
GLCM_HUMANGBAGlucosylceramidase42.42100.0472
DPYL3_HUMANDPYSL3Dihydropyrimidinase-related protein 3142.37680.0232
SPTB2_HUMANSPTBN1Spectrin beta chain, brain 1312.05120.0251
GDIR1_HUMANARHGDIARho GDP-dissociation inhibitor 182.01370.0105
ACADV_HUMANACADVLVery long-chain specific acyl-CoA dehydrogenase, mitochondrial71.87070.0486
ATPA_HUMANATP5A1ATP synthase subunit alpha, mitochondrial241.85350.0070
MYL6_HUMANMYL6Myosin light polypeptide 6161.78650.0487
LMO7_HUMANLMO7LIM domain only protein 7111.61440.0436
5NTD_HUMANNT5E5′-nucleotidase221.57040.0440
FLNA_HUMANFLNAFilamin-A1261.52760.0036
HS90A_HUMANHSP90AA1Heat shock protein HSP 90-alpha291.52760.0351
H32_HUMANHIST2H3AHistone H3.270.88720.0298
H2AJ_HUMANH2AFJHistone H2A.J70.77980.0365
PDLI7_HUMANPDLIM7PDZ and LIM domain protein 710.73110.0042
ALDR_HUMANAKR1B1Aldose reductase50.69180.0237
FLNC_HUMANFLNCFilamin-C140.63100.0145
MVP_HUMANMVPMajor vault protein230.56490.0078
VINC_HUMANVCLVinculin230.55460.0245
RS15A_HUMANRPS15A40S ribosomal protein S15a40.52480.0221
SFPQ_HUMANSFPQSplicing factor, proline- and glutamine-rich30.49660.0205
PLIN3_HUMANPLIN3Perilipin-3140.48750.0418
NNMT_HUMANNNMTNicotinamide N-methyltransferase60.47420.0400
1433Z_HUMANYWHAZ14-3-3 protein zeta/delta140.46990.0217
PRDX1_HUMANPRDX1Peroxiredoxin-1210.41690.0199
ANX11_HUMANANXA11Annexin A1190.37330.0014
G6PD_HUMANG6PDGlucose-6-phosphate 1-dehydrogenase150.36640.0006
HYEP_HUMANEPHX1Epoxide hydrolase 170.34670.0069
6PGD_HUMANPGD6-phosphogluconate dehydrogenase, decarboxylating100.29110.0040
CALU_HUMANCALUCalumenin140.26550.0057
NQO1_HUMANNQO1NAD(P)H dehydrogenase [quinone] 1110.25120.0153
TKT_HUMANTKTTransketolase210.14860.0051
ANXA5_HUMANANXA5Annexin A5380.12940.0002
ENOA_HUMANENO1Alpha-enolase540.10000.0419
ANXA2_HUMANANXA2Annexin A2740.08710.0019
IBP3_HUMANIGFBP3Insulin-like growth factor-binding protein 350.08020.0424
DEST_HUMANDSTNDestrin80.06140.0245
Note: Proteins are listed, according to fold change, in decreasing order. In bold, proteins previously related to the osteogenic process.
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Mucientes, A.; Herranz, E.; Moro, E.; González-Corchón, A.; Peña-Soria, M.J.; Abasolo, L.; Rodriguez-Rodriguez, L.; Lamas, J.R.; Fernández-Gutiérrez, B. Influence of Mesenchymal Stem Cell Sources on Their Regenerative Capacities on Different Surfaces. Cells 2021, 10, 481. https://0-doi-org.brum.beds.ac.uk/10.3390/cells10020481

AMA Style

Mucientes A, Herranz E, Moro E, González-Corchón A, Peña-Soria MJ, Abasolo L, Rodriguez-Rodriguez L, Lamas JR, Fernández-Gutiérrez B. Influence of Mesenchymal Stem Cell Sources on Their Regenerative Capacities on Different Surfaces. Cells. 2021; 10(2):481. https://0-doi-org.brum.beds.ac.uk/10.3390/cells10020481

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Mucientes, Arkaitz, Eva Herranz, Enrique Moro, Aranzazu González-Corchón, María Jesús Peña-Soria, Lydia Abasolo, Luis Rodriguez-Rodriguez, Jose Ramon Lamas, and Benjamín Fernández-Gutiérrez. 2021. "Influence of Mesenchymal Stem Cell Sources on Their Regenerative Capacities on Different Surfaces" Cells 10, no. 2: 481. https://0-doi-org.brum.beds.ac.uk/10.3390/cells10020481

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