The potential of MSCs in promoting bone repair has been promising, but there are still several factors that may limit their use and increase variability between studies. These include the source of MSCs, as well as the timing and quantity of implantation. Additionally, it is important to fully characterize the population of MSCs and determine the best approach based on the type and location of bone trauma or defect [
134]. In cases where in vitro expansion is necessary for cell transplantation or gene delivery purposes, limitations arise due to lack of standardization and automation in this process. Variability can occur depending on factors such as number of passages, media type, serum usage (including lot-to-lot variations), animal-free media availability or presence of xenogenic proteins which pose a risk for contamination. Similarly to other genetically modified cells, genetic modulation presents safety concerns particularly when viral vectors are used [
135]. Intrinsic biological variability between tissue sources, donors, clonal subsets, and single-cell variability, and extrinsically introduced variability through non-standard isolation, selection, and production methods result to MSC heterogeneity. Translation of MSC products beyond clinical trials has been limited due to, among other factors, MSC heterogeneity, complicating the ability to produce reliable, uniform therapy throughout the MSC expansion and banking process [
32]. Nevertheless, with the advancement of molecular biology techniques, there is an increasing possibility to utilize engineered MSCs or their secretome in clinical settings for addressing bone defects. The choice of biomaterials also affects treatment outcomes. The body's immune response to bone implants is influenced by a number of factors, including the macroporosity of the biomaterial, surface microstructure, material hardness, and particle size[
136,
137]. Macrophages are the main effector cells of the immune response to implants, and bone implants affect MSCs mainly in terms of cell viability, adhesion, migration, proliferation and differentiation[
138]. The presence of surface roughness in titanium, such as polished, machined, and grit-blasted commercially pure titanium, has been observed to impact the attachment and spreading of immune cells. Over time, macrophage adhesion increases on all surfaces while cell spreading is enhanced with higher surface roughness levels[
139]. Furthermore, the roughness of titanium can also influence the production of inflammatory cytokines and chemokines by macrophages. Significant stimulatory effects have been noted on sandblasted and acid-etched surfaces[
140], whereas titania nanotube arrays modified surfaces exhibit reduced immune response compared to raw titanium surfaces[
141]. It is worth noting that bone's surface roughness measures approximately 32 nm at a nanoscale level, making nanomaterials highly biomimetic[
142]. In vitro studies have demonstrated that nanoscale microstructures effectively stimulate human MSCs to produce bone minerals even without osteogenic supplements[
143]. Additionally, it has been discovered that macrophages exposed to microstructured topography become activated with both M1 and M2 characteristics instead of nanostructured topography alone[
144]. Research also indicates that perios-teal extracellular matrix (PEM) hydrogels promote the recruitment and M2-polarization of macrophages. They further facilitate differentiation of MSCs into endothelial-like cells along with HUVEC tube formation and osteogenic differentiation of MSCs[
145]. Therefore, new strategies that reduce MSC heterogeneity by pooled-MSCs, clonal MSCs, priming pretreatment of MSCs, biomaterial-MSC interactions and so on to improve their immunomodulatory potencies will clinically impact[
32,
146].
In the clinic, because bone marrow-derived MSCs are more difficult to collect and are themselves less abundant, studies of alternative sources have emerged[
147,
148,
149]. Some research results show that adipose MSCs and BM-MSCs have similar immunophenotypes and in vitro differentiation abilities, as well as similar immunomodulatory abilities, and that adipose MSCs are more metabolically active, secrete more cytokines, and are more efficient in their immunomodulatory effects than BM-MSCs. Adipose-derived stem cells (ASCs) can be considered as a good alternative to BM-MSCs for immunomodulatory therapy[
150]. ASCs are a significant subset of MSCs[
151]. ASCs, derived from the stromal vascular fraction (SVF), are progenitor cells located around blood vessels[
152]. Similar to BM-MSCs, ASCs have been extensively studied in the field of bone tissue engineering[
153]. ASCs possess the ability to differentiate into multiple cell lineages, including adipocytes, chondrocytes, and osteoblasts. The fate determination of these lineages is regulated by key factors such as Runx2 and Osterix (Sp7 transcription factor)[
125,
154]. Various signaling pathways play a crucial role in controlling osteogenic differentiation, including bone morphogenetic protein (BMP)[
155], Notch[
156], Wnt[
157] and Hedgehog-signaling[
158]. Among these pathways, Wnt signaling pathway acts as a pivotal regulator that directs ASCs differentiation towards osteogenesis by upregulating Runx2 and Osterix expression levels[
159]. Numerous studies have explored different substrates to enhance the osteogenic potential of ASCs. These substrates include vitamin D3 [
160], alendronate [
161], selenium [
162], platelet-rich plasma [
163], and the inflammatory response [
164,
165,
166,
167].
Pro-inflammatory cytokines secreted by macrophages (TNF-α, IL-6, IL-1β, IL-23, and IFN-γ) stimulate osteogenic differentiation of MSCs, and TGF-β and VEGF have been shown to have angiogenic activity. PGE2 and IL-4 secreted by MSCs induce the transformation of macrophages from M1 type to M2 type. MSCs affects DCs differentiation and proinflammatory cytokine secre-tion through TGF-β1, IL-6 and GRO-γ. MSCs not only stimulate T cell apoptosis through Fas/FasL pathway and PD-L1 secretion, MSCs can also secrete heme oxygenase-1 (HO-1) and IL-10, up-regulate the PD-1 receptor on Tregs, and trigger the immunosuppressive ability of Tregs. Meanwhile, activated T cells induced MSCs apoptosis via the Fas/FasL and CD40/CD40L pathways. However, Tregs are able to shed large amounts of TNF receptor superfamily member 1B (TNFRII) and thus inhibit the ac-tion of TNF and promoting bone formation, IL-17A secreted by γδT cells shifts the lipid differentiation capacity of MSCs to osteogenic differentiation, there-by improving the quality of bone healing. TGF-β and IL-6 produced by activated MSCs limit NK cell effector function but promote NK cell differentiation. The inhibition of B cell activation by MSC depends on IFN-γ and PD-1/PD-L1.