Investigating the mechanophysical and biological characteristics of therapeutic dental cement incorporating copper doped bioglass nanoparticles
Graphical Abstract
Introduction
Dental types of cement have been widely applied in the field of restorative and orthodontic dentistry such as in cavity linings, sedative filling, temporary or permanent tooth restorations, and the joining of fixed prostheses and orthodontic band [1], [2], [3], [4], [5], [6]. In particular, ‘ideal’ dental cement should have several characteristics: nonirritant, good resistance to dissolution in saliva and oral fluids, high mechanical strength, adequate working and setting time, and low film thickness (≤ 25 µm) for luting agent [7], [8], [9], [10]. Cement that satisfy the aforementioned properties can be classified as zinc phosphate, polycarboxylate, zinc oxide eugenol, glass ionomer, and resin-modified glass ionomer cement [6], [11], [12], [13], [14], [15]. Despite the advent of new cement such as glass ionomers or resin-based cement, many clinicians prefer zinc phosphate cement (ZPC) for luting cast metal prostheses because of its ease of operation, high elasticity and compressive strength, optimum coating degree, ease of excess cement removal, and cost-effectiveness [3], [16], [17]. Moreover, it has been indicated that the high stiffness of ZPC materials could be beneficial for reducing stresses transmitted from the restoration as a base material in the cavity [18]. However, deficiencies of ZPC include low antibacterial activity, the probability of pulp irritation due to the low pH at the beginning of hardening, no chemical adherence to teeth, and relatively high solubility in the oral cavity [3], [19]. Little has been applied to overcome these limitations of ZPC, although many researchers have attempted to improve the properties of cement biomaterials by adding micro/nanoparticles as reinforcements or therapeutic fillers such as graphene oxide, and bioactive glasses [20], [21], [22], [23], [24].
Bioactive glasses (BGs) were first introduced in 1969 by Hench as a promising biomaterial for application in tissue regeneration [25]. A range of bioactive materials with attractive properties, such as biocompatibility and bioactivity, synthesized by novel methods have been investigated [25]. Recently, bioactive glass nanoparticles (BGn) have stood out as excellent candidates for nanostructured composites, as their small size, high surface area to volume ratio and uniformity in shape facilitate a more homogeneous distribution in comparison to their micronsized-counterparts [26], [27], [28]. The addition of BGn to other materials may exhibit synergistic effects combining osteogenic potential and satisfactory mechanical properties through the release of therapeutic metallic ions [26]. Among the variety of therapeutic ions, copper (Cu) ion-containing bioglass nanoparticles (Cu-BGn) have been proven to be able to enhance hard tissue regeneration and vascularization as well as wound healing [29], [30], [31], [32]. Additionally, Cu-BGn is recognized to be antimicrobial, a crucial aspect for effective hard tissue repair under bacterial infection, which can be induced by the release of copper ions from the nanoparticles [33], [34]. As an example, we reported that copper added to bioactive glass nanoparticles or Cu-incorporated bioactive glass nanoparticles (Cu-BGn), not only contributed to angiogenesis but also showed antibacterial activity against E. faecalis, which is frequently accompanied by pulp infections [35].
Recently, Wassmann et al. used commercial Cu-modified zinc phosphate cement (Hoffmann’s copper cement, Hoffmann’s Dental Manufacturer, Germany) to evaluate antimicrobial activities and mechanical properties [19]. They did not find enhanced antimicrobial activities in Cu-modified zinc phosphate cement, probably due to inhomogeneity or the concentration of Cu [36], [37]. To our knowledge, including the above literature, the effect of Cu-modified ZPC has rarely been investigated in terms of odontoblastic differentiation for minimizing pulp irritation. Previously, inorganic cements (e.g., strontium-releasable inorganic, calcium silicate-based, and hydroxyapatite-based cements) have been reported [38], [39], [40]. Unlike commercial Cu-modified zinc phosphate cement, inorganic dental cements have promoted odontogenic differentiation as well as shown antibacterial properties due to the released therapeutic ions.
In this study, we propose a novel Cu-doped bioglass nanoparticles (Cu-BGn) that incorporated onto the ZPC (Cu-ZPC) as a dental cement because Cu-BGn has potential to release therapeutic ions such as Cu, Ca, and Si. To obtain stable Cu-ZPC, the Cu-BGn concentration was optimized based on film thickness and net setting time. The overall characteristics of the optimized Cu-ZPC were compared with those of Cu-free-ZPC by manipulating the mechanophysical properties, such as compressive strength, hardness, and roughness, as well as the biological properties, including cell viability, odontoblastic activities, and antibacterial properties, against dental pulp human cells. The null hypothesis of this study is that there would be no significant differences in the 1) mechanophysical properties and 2) in vitro cellular activations between Cu-ZPC and bare ZPC.
Section snippets
Preparation of Cu-BGn and Cu-BGn-added zinc phosphate cement (Cu-ZPC)
Cu-BGn was prepared based on a previous study [41]. Briefly, 5 g of copper (Sigma–Aldrich, USA) was dissolved in 120 mL of alkaline methanol (pH = 12.5), and calcium nitrate tetrahydrate (Ca (NO3)4·4H2O, 99%, Sigma–Aldrich, USA) was added. In a separate batch, tetraethylorthosilicate (TEOS, 99%, Sigma–Aldrich, USA) was homogeneously dissolved in 30 mL of absolute methanol (pH = 12.5) and added to the first solution with the simultaneous application of ultrasonic homogenizers (SONOPULS). The
Results
The fabrication of copper bioglass nanoparticles (Cu-BGn) via a sol-gel method is represented schematically in the Fig. 1A. Following condensation, gelation, and drying, a homogeneous Cu-BGn powder was obtained. The morphology and crystal structure of Cu-BGn powder was characterized by FE-SEM imaging and X-ray diffraction (XRD) (Fig. 1B, C). Additionally, the representative EDS spectra showed a chemical composition of 9.28 ± 0.4% Cu, 5.89 ± 0.8% Ca, and 84.83 ± 0.4% Si (wt%) (Fig. 1D).
Discussion
Our hypothesis is that there are no significant differences in the 1) mechanophysical properties and 2) in vitro cellular activations among each group because of the low amounts of additives (2.5 wt% Cu-BGn) in ZPC. The mechanophysical properties (e.g., compressive strength, compressive modulus, surface roughness, and hardness tests) had no significance among the groups, and the first null hypothesis was approved. Unlike the mechanophysical properties, in vitro tests (e.g., cell viability,
Conclusion
In this study, we fabricated Cu-ZPC consisting of 2.5 wt% Cu-BGn incorporated into ZPC. By manipulating the mechanophysical characteristics by adjusting the Cu-BGn concentration, the film thickness, net setting time, compressive strength, compressive modulus, hardness, and surface roughness were optimized according to the International Organization of Standards (ISO). For applications in odontoblastic activations, biological activations (e.g., cell viability, ALP activity, ARS staining, and
Acknowledgments
This work was supported by a National Research Foundation of Korea (NRF) grant funded by the Global Research Development Center Program (2018K1A4A3A01064257), by the Medical Research Center Program (2021R1A5A2022318), by the Ministry of Science and ICT (2019R1C1C1002490, 2020R1A2C1005867) and by the Priority Research Center Program provided by the Ministry of Education (2019R1A6A1A11034536). Additionally, this work was supported by a National Research Foundation of Korea (NRF) grant funded by
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These authors contributed equally to this work as first authors.