Nanoparticles And Human Saliva: A Step Towards Drug Delivery Systems For Dental And Craniofacial Biomaterials
Received 2 July 2019
Accepted for publication 27 September 2019
Published 27 November 2019 Volume 2019:14 Pages 9235—9257
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Editor who approved publication: Prof. Dr. Thomas J. Webster
Rafal Pokrowiecki,1–3 Jacek Wojnarowicz,4 Tomasz Zareba,2 Iwona Koltsov,4 Witold Lojkowski,4 Stefan Tyski,2,5 Agnieszka Mielczarek,6 Pawel Zawadzki1
1Department of Cranio-Maxillofacial Surgery, Oral Surgery and Implantology, Medical University of Warsaw, Warsaw, Poland; 2Department of Antibiotics and Microbiology, National Medicines Institute, Warsaw, Poland; 3Private Practice, Warsaw, Poland; 4Institute of High Pressure Physics, Polish Academy of Sciences, Warsaw, Poland; 5Department of Pharmaceutical Microbiology, Medical University of Warsaw, Warsaw, Poland; 6Department of Conservative Dentistry, Medical University of Warsaw, Warsaw, Poland
Correspondence: Agnieszka Mielczarek
Department of Conservative Dentistry, Medical University of Warsaw, Binieckiego 6, Warsaw 02-097, Poland
Tel +48 22 116 6446
Fax +48 572 0154
Email [email protected]
Aim: The aims of this study were to investigate new nano-formulations based on ZnO and Ag nanoparticle (NP) compounds when used against clinical strains of oral gram-positive and gram-negative bacteria, and to examine the stability and behaviour of nano-formulation mixtures in saliva based on different compositions of Ag NPs, ZnO NPs and ZnO+x·Ag NPs.
Methods: ZnO NPs with and without nanosilver were obtained by microwave solvothermal synthesis. Then, antibacterial activity was evaluated against bacteria isolated from human saliva. Behavior and nanoparticle solutions were evaluated in human saliva and control (artificial saliva and deionized water). Results were statistically compared.
Results: The NP mixtures had an average size of 30±3 nm, while the commercial Ag NPs had an average size of 55±5 nm. The suspensions displayed differing antibacterial activities and kinetics of destabilisation processes, depending on NPs composition and fluid types.
Conclusion: The present study showed that all NPs suspensions displayed significant destabilisation and high destabilisation over the 24 h of the analyses. The agglomeration processes of NPs in human saliva can be reversible.
Keywords: nanomaterials, controlled drug release, nanoparticles, metal nanoparticles, bacteria
Metallic and non-metallic biomaterials are widesNPread in contemporary regenerative medicine, and are used to help recreate missing tissues. As a favourable niche for bacterial settlement and biofilm formation, they carry an increased risk of bacterial and fungal infection, which may lead to severe complications and an increase in patient morbidity. This is most commonly seen in patients treated with partially external metallic biomaterials. The majority of these are used in the treatment of orofacial trauma, congenital or acquired morphologic diseases, tumours and much more. In most cases, peri-implant infections lead to local or general complications, such as non-unions, abscesses, osteomyelitis or even septicaemia and death. In general, empiric antibiotic therapy is commonly applied as an accompanying treatment procedure related to implant infection. However, due to the extreme resistance of the biofilm to drugs and the host’s immune system, biomaterial-associated infections have significantly contributed to the global increase in bacterial resistance to widely used antibiotics over the past 30 years.1 Despite the efforts being made in treatment modalities, in most cases the infected material must be removed in order to decrease the risk of septicaemia and patient death. As orofacial infections are most often inadequately treated by means of antibiotics, their overuse has contributed significantly to the global increase in multi drug resistant (MDR) species. As the 21st century has been called the “post-antibiotic era”, new approaches are needed for infection prevention and treatment. In recent years, nanomaterials have entered the dental market as promising alternatives for their older counterparts, giving rise to a new field of science described as “nanodentistry”.2,3 This approach assumes two major breakthroughs. One is associated with an improvement in the biomechanical properties of the restoration materials, and the other in providing new solutions to the current limitations associated with implant-derived drug delivery.4 The release of NPs or their ions into the environment has been described as the most important factor contributing to broad antibacterial activity, increasing the longevity of the biomaterial within the tissues. There are some reports available on the antibacterial activity of nanoparticles against oral pathogens, but the results are extremely diversified. Confounding effects are often caused by significant discrepancies between the in vitro and in vivo environments. The oral cavity is a distinct ecosystem which significantly differs from all others in the human body. The presence of protein- and sugar-rich saliva and bacteria, which cover all surfaces in the mouth, exerts an important effect on drug pharmacokinetics and bioavailability. It was shown that nanoparticles released into the oral cavity may change their physicochemical properties by the formation of a protein corona (PC). Such fluctuations in the chemical composition of biomolecules may significantly contribute to the material’s antibacterial activity and toxicity to human tissues as well. The potential for carcinogenic effects cannot be neglected. Moreover, it is known that bacteria can develop resistance to NPs as well, when they are applied incorrectly, especially in the oral cavity.5 Therefore, in order to fully comprehend the tasks associated with estimating the bio-safety of different NPs in clinical use, the phenomena influencing NPs activity in the specific biological environment must be evaluated in more detail.6,7 This process describes the changes in the physicochemical properties of the given NPs in certain biological fluids, determining NPs antimicrobial activity and toxicity in vivo, which may differ significantly from results obtained in vitro.3,8–11 There are several reports on the interaction of NPs with human blood serum,12 but studies investigating the behaviour of certain NPs in human saliva, their potential effect on the tissues of the oral cavity, their diffusion through the mucosa and their impact on vital organs remain in the initial phases.13,14
In recent years, nano zinc oxide (ZnO) and nanosilver (Ag) have attracted enormous interest in pharmacy and biomedicine thanks to their antibacterial properties.15,16 Due partly to its bleaching and matting properties, ZnO is used in the production of creams, dressings, powders, baby powders and specialist toothpastes. ZnO is a popular mineral UV filter used in cosmetics that offer sunlight protection. Research is being carried out on the application of ZnO nanostructures in biomedical imaging, drug delivery, gene delivery, biosensing and denture modification.17–22 Ag NPs, mainly thanks to their antibacterial action,5,23,24 are already applied in such products as dressings, toothpastes, cosmetics, materials intended for contact with food, textiles (e.g. socks) and shoes.25,26 In the case of Ag nanostructures, research is being conducted on a variety of applications, such as for the creation of novel antimicrobial coatings and agents, drug-delivery formulations, detection and diagnosis platforms, tissue restoration, regeneration materials and denture modification.27–33
The aim of this study is to investigate new nano-formulations based on two of the most commonly applied dental materials: zinc oxide nanoparticles (ZnO NPs) and silver nanoparticles (Ag NPs), compounds used against clinical strains of oral gram-positive and gram-negative bacteria. Additionally, the evaluation of the release profiles and the formation of nanoparticle-protein-sugar complexes in the saliva and human serum will be a first step toward better understanding of NPs behaviour in a biological environment and how NP-protein complexes may contribute to potential cytotoxicity. The verification of the hypothesis should outline future directions in the field of dental nano-biomaterials and provide better insight into antibacterial approaches against nosocomial infections in regenerative medicine of the head and neck. Finally, it should provide important information on reliable ways to reduce the development of global bacterial resistance to the currently overused antibiotics, especially those used in odontogenic infections.
Materials And Methods
Patient Selection And Saliva Sampling
A total of 30 patients aged 18–53 years (15 males, 15 females), treated due to dental caries at the Department of Conservative Dentistry, Warsaw Medical University, were randomly selected for stimulated saliva sampling. This study was conducted in accordance with the Declaration of Helsinki. All the patients received and signed the patient informed consent, and the study was approved by the Warsaw Medical University Ethical Committee, ref no. KB/150/2018. The patients refrained from eating, drinking and using mouth-cleaning products 2 hrs prior to saliva collection. Then the patients were asked to chew on a paraffin gum and deposit a total volume of 6 mL of saliva in three 2 mL Eppendorf tubes (Oral Swab Collection Kit, Salimetrics, USA). Then, after the collection, the samples were transported (Cryovial 2 Cryostorage Box, Salimetrics, USA) for further research to the Department of Antibiotics and Microbiology, National Medicines Institute, Warsaw, Poland (2 mL sample from each patient) and the Laboratory of Nanostructures, Institute of High Pressure Physics (UNIPRESS), Polish Academy of Sciences (4 mL sample from each patient).
Preparation Of Nanoparticles And Their Solutions, Methods
The following reagents were used: zinc acetate dihydrate (Zn(CH3COO)2∙2H2O, Zn(Ac)2∙2H2O analytically pure, Chempur, Poland); silver acetate anhydrous (Ag(CH3COO), Ag(Ac), analytically pure, Chempur, Poland); ethylene glycol (EG, ethane-1,2-diol, C2H4(OH)2, pure, Chempur, Poland); Ag-NPs (Hydro Silver 1000 (55±5 nm, PVA coating, water suspensions, 1000 ppm), Amepox, Łódź, Poland);34 deionized water (H2O) (specific conductance below 0.1 µS/cm, HLP 20UV, Hydrolab, Poland); artificial saliva for medical and dental research (Pickering Laboratories, Inc., Mountain View, California, USA). The reagents were not purified and were used “as received”.
Synthesis Of ZnO NPs And ZnO+x·Ag NPs
ZnO NPs were obtained by the microwave solvothermal synthesis (MSS) in accordance with the procedure we established35–38 while ZnO+x·Ag NPs were created for the first time with the use of MSS. The composition of the precursors determined by equation (1)38 is summarized in Table 1.
Table 1 Composition Of Precursors Of Synthesis Of ZnO NPs And ZnO+x·Ag NPs
The mixture of the acetates in EG (300 mL) was stirred (450 rpm) at a temperature of 70°C using hot-plate magnetic stirrers (SLR, SI Analytics, Germany) until complete dissolution. Subsequently, each obtained precursor solution was poured into a bottle (500 mL, PP) and sealed. Once the solutions achieved ambient temperature, their initial H2O content was determined. Later, calculated quantities of H2O were added to the solutions so that the final concentration of 2 wt% could be achieved in each precursor solution, which was confirmed by analysis.
The syntheses were performed in a microwave reactor, model MSS2 (“cup” chambers, 400 mL, 3 kW, 2.45 GHz, IHPP PAS, ITeE-PIB, ERTEC-Poland).39,40 The synthesis parameters were as follows: feedstock volume 270 mL, reaction duration 12 mins, microwave power 1kW. The obtained suspensions were centrifuged (MPW-350, MPW Med Instruments, Poland) in order to separate the solid synthesis product from the EG The sediments were rinsed three times with deionized water and subsequently H2O was added to the sediments, characterized by a paste consistency and stirred intensively to obtain suspensions. 40 mL of the suspension was collected from each sample, frozen using liquid nitrogen and dried in a freeze dryer (Lyovac GT-2, SRK Systemtechnik GmbH, Germany).
Characterization Of NPs
The full description of the measurement procedures used is included in the publication.36 The concentration by weight of the water in the precursor solutions was determined using the coulometric titration technique, based on the assumptions of the Karl Fischer method (Cou-Lo AquaMAX KF, GR Scientific, United Kingdom).
The phase composition of the NPs samples was determined by the X-ray diffraction method (XRD) (X’Pert PRO, copper lamp (CuKα), Panalytical, Netherlands). The diffraction analyses were performed in 0.02° steps within the range of the 2-theta angle, from 10° to 100°, at room temperature. Scherrer’s formula was used to determine the average crystallite size.35 Thanks to the analysis of the diffraction peak profile by the FW15/45M method,41 which was used in the Nanopowder XRD Processor Demo web application, the average crystallite size,42,43 the deviation of the average crystallite size and the crystallite size distribution were determined.
The NPs samples for the density and specific surface area tests were desorbed in a VacPrep 061 (Micromeritics®) degassing station for 2 h (0.05 mbar, 150°C). The skeleton density (pycnometric density) was determined using a helium pycnometer (24±1°C, ISO 12154:2014, AccuPyc II 1340, FoamPyc V1.06, Micromeritics®, USA). The specific surface area was determined by the nitrogen (99.999% N2) adsorption method based on the linear form of the BET (Brunauer-Emmett-Teller) isotherm equation (ISO 9277:2010, Gemini 2360, V 2.01, Micromeritics®, USA). The average size of the NPs was calculated based on the obtained results of density and specific surface area, assuming that the samples contained only identical spherical particles.35
The morphology of the NPs was tested using a scanning electron microscope (SEM) ULTRA PLUS (ZEISS, Germany). The quantitative X-ray microanalysis of the zinc and silver content of the pressed samples (pastilles with a 5mm diameter) was performed by the energy-dispersive spectrometry (EDS) method using an X-ray spectrometer (Quantax 400, Bruker, USA). The results of the quantitative analysis of zinc and silver presented here are the averaged values from 5 analyses.
A Bruker Tensor 27 infrared spectrometer, equipped with an Attenuated Total Reflectance (ATR, model: Platinum ATR-Einheit A 255), was used for the Fourier transform infrared (FT-IR) spectroscopy analysis (50 scans, range of 400–4000 cm−1, resolution of 4 cm−1, room temperature).
The samples of 5 NPs suspensions, each of 100 mL and concentration of 1000 ppm before DLS measurement, were subjected to the ultrasonic homogenization process (UP200, Hielscher, Teltow, Germany) with the following parameters: duration 3 mins, amplitude 0.7, cycle 1, sonotrode diameter 14 mm, without temperature stabilization. The homogenized suspensions, having achieved a room temperature of 22.9°C, were added in appropriate quantities to H2O, artificial saliva or human saliva to obtain the final concentration of 200 ppm.
Collection Of Oral Bacteria And Preparation For The Studies
The antimicrobial activity of the synthesised NPs was evaluated by the standardised pharmaceutical methods of drug testing commonly performed at the National Medicines Institute, Warsaw, Poland (accredited OMCL) against clinical isolates and standard strains of the bacteria and fungi isolated from the sampled saliva. The tests were performed according to the modified method recommended by the Clinical and Laboratory Standards Institute (CLSI), such as the M100 Performance Standards for Antimicrobial Susceptibility Testing, M02 Performance Standards for Antimicrobial Disk Susceptibility Tests and M07 Methods for Dilution Antimicrobial Susceptibility Tests for Bacteria That Grow Aerobically, commonly used in the determination of antimicrobial susceptibility.
Clinical isolates of Streptococcus Salivarius; S. oralis; S. mutans; S. mitis and Porphyromonas gingivalis; were sub-cultured, divided and grouped. S. salivarius, S. oralis, S. mutans and S. mitis were prepared using an overnight culture in Tryptic Soy Broth (TSB; Biomerieux), supplemented with a 10% yeast extract (Roth, Karlsruhe, Germany) under aerobic conditions at 37°C for 24 h. Porphyromonas gingivalis were prepared by culturing for 48 h on a brain heart infusion medium (BHl; Oxoid, Wesel, Germany), supplemented with 10 μg/mL of vitamin K (Roth, Karlsruhe, Germany) under anaerobic conditions (80% N2, 10% H2, 10% CO2) at 37°C for 48 h.
Antibacterial Activity Of Nanoparticles Against Oral Cavity Bacteria
In order to evaluate the antimicrobial activity of the nanoparticles and nanomaterials, minimum inhibitory concentration (MIC) values were measured by means of broth micro-dilution tests in 96-well microtiter plates. S. salivarius, S. oralis, S. mutans and S. mitis were cultured in the presence of the NPs at respective concentrations (Table 1) in BHI broth under aerobic conditions at 37°C for 24 h. P. gingivalis was cultured in the presence of NPs in CDM supplemented with 10% human serum under anaerobic conditions (80% N2, 10% H2, 10% CO2) at 37°C for 72 h. Each test was performed in triplicate. The results were statistically analysed using Pearson’s Chi square tests (STATISTICA12 PL). A P value of 0.05 was considered statistically significant for all tests.
Behaviour Of Nanoparticles And Their Solutions In Human Saliva
The average ZnO particle size was measured by the dynamic light scattering (DLS) method (λ=633 nm, Zetasizer Nano-ZS ZEN 3600, Malvern Instruments Ltd., UK). The DLS measuring system with the automatic sample collection function comprised the following components: DLS analyser, titrator with magnetic stirrer and peristaltic pump, container for NPs suspensions, silicone hoses for supplying and discharging the suspension and a folded capillary cell (DTS1060 cuvette). The tests were carried out with the following parameters: 24°C temperature and 173° measurement angle (backscattering), analysis model: auto mode, 6 measurements. A fresh portion of the sample was pumped once every hour to a DTS1060 measurement cuvette by the titrator (MPT-2, ZEN1001, Malvern Instruments Ltd., UK) for 24 h. It must be underlined that the suspension sample was stirred using the magnetic stirrer in the MPT-2 titrator for the whole test duration. Zetasizer 7.11 software was used (Malvern Instruments Ltd).
The zeta potentials (ζ) of the samples were measured using a laser Doppler electrophoresis (LDE) analyser (λ=633 nm, Zetasizer Nano ZS ZEN3600, Malvern Instruments Ltd). The tests were performed in DTS1060 cuvettes with the following parameters: 24°C temperature, analysis model: auto mode, 6 measurements.
The pH measurement at room temperature (23.2°C) was performed using an ERH-12-6 electrode (Hydromet, Gliwice, Poland) installed in the MPT-2 titrator. Three buffer solutions (Chempur, Piekary Slaskie, Poland) with a pH of 4±0.05, 7±0.05 and 9±0.05 were used for calibrating the pH electrode.
The specific conductivity (σ) measurement at room temperature (23.2°C) was performed using an InLab 731-ISM conductivity probe (Mettler-Toledo, Greifensee, Switzerland) installed in a S400 Seven Excellence instrument (Mettler-Toledo, Greifensee, Switzerland). A conductivity standard (1413 µS, Mettler-Toledo, Greifensee, Switzerland) was used to calibrate the conductivity probe.
The stability measurement was carried out by the static multiple light scattering (S-MLS) method,44,45 applied in a Turbiscan LAB analyser (λ=880 nm, Formulaction, Toulouse, France). The samples were analysed in a sealed cylindrical glass bottle (4 mL, 14.7 mm outer diameter). The measurements were performed over 24 h hours at a temperature of 27°C. Based on the data gathered by the Turbiscan LAB analyser, the Turbiscan Stability Index (TSI) was calculated,46,47 which is a unique parameter established for the comparison and characteristics of physical stability of various suspensions.48,49
The results were statistically analysed using One Way Anova (STATISTICA12 PL). A P value of 0.05 was considered statistically significant for all tests.
Characteristics Of NPs
The results of the XRD tests (Figure 1) for the ZnO NPs sample revealed the presence of only one crystalline phase, where all the diffraction peaks were attributed to the hexagonal phase of ZnO (JCPDS No. 36–1451). The results of the XRD tests (Figure 1) for all samples with the addition of silver indicated the presence of two crystalline phases, namely the hexagonal phase of ZnO (JCPDS No. 36–1451) and the cubic phase of Ag (JCPDS No. 04–0783). The diffraction pattern showed an increase in intensity of certain diffraction peaks in line with the increase in the Ag content in the samples, which confirmed that the synthesis method we developed leads to the formation of two different products. The obtained XRD results proved that the Ag+ ions were not incorporated into the crystalline lattice of ZnO, but during the synthesis were reduced to metallic Ag° and the obtained product of the microwave solvothermal synthesis was a mixture of ZnO NPs with Ag NPs.
Figure 1 X-ray diffraction patterns of ZnO NPs and ZnO+x·Ag NPs. Abbreviations: ZnO, zinc oxide; Ag, silver; NPs, nanoparticles; JCPDS, Joint Committee on Powder Diffraction Standards; a.u., arbitrary unit.
Figure 2 shows representative SEM images of the obtained samples. The powders of the nanoparticles of ZnO, ZnO+0.1%Ag and ZnO+1%Ag were composed of homogeneous particles with a spherical shape, while a small quantity of particles with an elliptical shape were observed in the SEM images (Figure 2B, D and F). The ZnO+10%Ag sample shown in Figure 2G was composed mainly of compact structures, whose shape resembled a “cauliflower” structure. The size of the NPs for all samples ranged from 20–30 nm to 60–90 nm.
Figure 2 SEM photographs of ZnO+x·Ag with varying silver content: (A) and (B) 0%Ag; (C) and (D) 0.1%Ag; (E) and (F) 1%Ag; (G) and (H) 10%Ag. Abbreviations: SEM, scanning electron microscope; ZnO, zinc oxide; Ag, silver.
Figure 3 shows SEM photographs taken using the angle-sensitive backscatter (AsB) detector, thanks to which the agglomerates/aggregates of Ag NPs could be discerned among the nanoparticle mixture. In order to confirm that the white fields visible in the SEM photographs (Figure 3) were agglomerates/aggregates of Ag NPs, mapping of the elements was carried out using the EDS method.
The most important results of the characterization of the obtained NPs samples are summarized in Table 2. The difference between the theoretical density of Ag (10.50 g/cm3)50 and the theoretical density of ZnO (5.61 g/cm3)51 explains the increase in density of the samples from 5.31 to 5.82 g/cm3 in line with the increase in the silver content from 0% mol to 10% mol. The specific surface area first increased from 34.6 m2/g to 37.7 m2/g in line with the increase in the Ag content from 0% mol to 0.1% mol, and subsequently decreased to 31.4 m2/g in line with the increase in the Ag content to 10% mol. The change in the specific surface area trend was probably caused by the formation of a greater quantity of aggregates of Ag NPs in line with the increase in the Ag content in the samples. The tendency of unmodified Ag NPs for rapid agglomeration/aggregation is widely known. While preparing the samples, no surfactants were used for modifying the surface of the NPs, which would prevent the agglomeration or aggregation process.52
Table 2 Characteristics Of NPs
The average particle size calculated based on the conversion of the density and specific surface area results for all synthesized samples ranged from 30 to 33 nm. The average crystallite size, in turn, calculated using the Nanopowder XRD Processor Demo application for all samples ranged from 28 to 29 nm. It must be emphasised that the average ZnO crystallite size calculated based on Scherrer’s formula for the samples with an Ag content from 0% to 1% was 30–31 nm, while for the ZnO+10%Ag sample merely 16 nm. The difference in the size of the obtained ZnO crystallites in the ZnO+10%Ag was caused by the simultaneous synthesis of ZnO NPs and Ag NPs, which, given the 10% silver acetate content relative to the zinc acetate, contributed to the change in the course of ZnO NPs growth.36 The calculated size of the Ag crystallites was 35 nm and 39 nm for the ZnO+1%Ag and ZnO+10%Ag samples, respectively. For the ZnO+0.1%Ag sample, it was impossible to calculate the crystallite size due to the low intensity of the diffraction peaks. A virtually identical crystallite size distribution was obtained for three samples, which ranged from ≈7 nm to ≈70 nm (Figure 4A–C), while for the ZnO+10%Ag sample the distribution ranged from ≈2 nm to ≈85 nm (Figure 4D).
Figure 4 Crystallite size distribution obtained using Nanopowder XRD Processor Demo, pre.α.ver.0.0.8, © Pielaszek Research.38,41Abbreviations: XRD, X-ray diffraction; ZnO, zinc oxide; Ag, silver; a.u., arbitrary unit; nm, nanometer.
The actual chemical composition of the samples is summarised in Table 3. While calculating the nominal silver content, we assumed that the Ag+ ions would constitute an admixture in the crystalline lattice of ZnO and ignored the oxygen share in the calculations. As indicated by the XRD and SEM analyses, the obtained synthesis product was a mixture of ZnO NPs and Ag NPs, and therefore the actual Ag content was lower than the nominal one. We used nominal silver contents for the purposes of naming the samples in the whole paper.
Table 3 Results Of The Chemical Composition Of NP Samples By The EDS Method
Among all the tested nanoparticles and their compounds, Ag NPs (hydrosilver) was the most efficient, providing MICs against all tested bacteria, even at a concentration of 1 ppm (p= 0.000). The minimum inhibitory concentrations for ZnO NPs were 125 ppm against all oral streptococci, with no significant differences between the species, and ranged from 125 to 250 ppm against anaerobic species without significant differences between species (Figure 5). For the ZnO+0.1%Ag, ZnO+1%Ag and ZnO+10%Ag samples, antibacterial concentrations providing MICs ranged from 32 to 64 ppm against all the tested bacteria, regardless of silver percentage. However, regardless of silver percentage, the antibacterial potential of zinc oxide NPs increased significantly. The antibacterial susceptibility to certain NPs was comparable between bacterial species. Only 5C species were significantly more susceptible to the NPs tested among all oral bacterial species (Supplementary materials).
Figure 5 A categorized histogram of the overall percentage of inhibited (NO) and grown (YES) bacterial species depending on the type of solution used: (A) ZnO NPs, (B) ZnO+0.1%Ag, (C) ZnO+1%Ag, (D) ZnO+10%Ag, (E) Ag (Figures S16 and S17). It can be seen that only pure Ag NPs (E) provided significant antibacterial properties against all tested oral bacteria (p= 0.000). Abbreviations: ZnO, zinc oxide; Ag, silver.
Nanoparticles And The Biological Fluids
Table 4 summarises the analysis results of the NP suspensions, performed once they were obtained (t=0h). For the ZnO, ZnO+0.1%Ag and ZnO+1%Ag samples, very similar results for average particle size were obtained, ranging from 114 nm to 145 nm. The average agglomerate size for the ZnO+10%Ag sample was 667 nm, while for the Ag NPs sample it was 239 nm. After adding the NPs to the artificial saliva, a considerable and rapid growth of agglomerates occurred in all the obtained samples. The impact of the Ag NP content in the suspensions on the average size of the obtained NP agglomerates was visible, i.e. the higher the Ag NP content in the ZnO+x·Ag suspension, the larger the agglomerates obtained (Table 4). The average agglomerate size for the Ag NPs sample was 2162 nm, and was comparable to the average size for the ZnO+1%Ag sample. In the suspension obtained in human saliva, the size of the ZnO, ZnO+0.1%Ag and ZnO+10%Ag agglomerates was about 340–380 nm, while the agglomerate sizes for the ZnO+10%Ag and Ag NPs samples were 563 nm and 616 nm, respectively. It must be underlined that the average size determined by the DLS method refers to the diameter of the sphere, which is the so-called hydrodynamic diameter, while the obtained result is the average size of the particles, agglomerates and aggregates. Therefore, when the tested NPs/agglomerates/aggregates deviated from the adopted shape assumptions, an increase in the standard deviation and in the polydispersity index was observable for the tested samples.
Table 4 Obtained Suspensions Of Nanoparticles And Their Characteristics Prior To Testing (Time 0 h)
The obtained value of ZnO NPs zeta potential in deionised water for pH≈7 was identical to that reported in the literature, i.e. approx. 35 mV.54 The appearance of Ag NPs in the ZnO NP suspension caused a fixed and declining trend in the zeta potential value up to 0.5 mV for the ZnO+10%Ag sample. The zeta potential of the Ag NPs sample in the deionized water was −2.2 mV. It is assumed that the prerequisite for the stability of water dispersion of the particles (if spherical stabilisation does not work) is a zeta potential higher than |30 mV|.55 If the zeta potential ranges from −30mV to 30 mV, then the NPs display an agglomeration tendency. The point at which the zeta potential reaches zero and changes its sign is called the isoelectric point. At this point, dispersion is not characterised by electrostatic stability. The zeta potential for the NPs in artificial saliva exceeded |30 mV| for the ZnO, ZnO+0.1%Ag, ZnO+1%Ag and ZnO+10%Ag samples, i.e. they fell within the range of the theoretical electrostatic stability. The only exception here was the Ag NPs sample, where the zeta potential value in artificial saliva was approx. −22mV. For suspensions obtained in human saliva, the zeta potential value was below |30 mV| for all samples, i.e. within the range of a lack of electrostatic stability. According to the adopted range of stability, due to the zeta potential value, all samples of ZnO+x·Ag NPs in artificial saliva should form stable suspensions; however, the average particle size results did not show this (Table 4). The process of NPs agglomeration at the moment of their introduction to artificial saliva could have been caused by:
- a high concentration of ions (e.g. Na+, K+, Ca2+, Mg2+, Cl−, SO42−, PO43−, CO32−, SCN−), which resulted in a small range of electrostatic repulsion energy by electric field screening; - the presence of macroparticles (proteins, carbohydrates) with multiple functional groups, such as –OH, -COOH, -NHx, -SH, in the saliva, which caused the formation of hydrogen bonds (also known as hydrogen bridges) between the particles/macroparticles and the various molecules.
Each of the prepared nano-formulations exhibited significant changes when exposed to the tested media. It could be seen that in the deionised water, and in both the artificial and human saliva, the nanoparticles tended to agglomerate with time (Figures 6–8). The patterns of agglomeration were remarkably diversified between the media, though. When exposed to artificial saliva, immediate agglomeration occurred in all the tested materials and continued over the 24 h incubation period.
Figure 6 Results of the study of average size of NPs in deionised water as a function of time. Abbreviations: ZnO, zinc oxide; Ag, silver; nm, nanometre; h, hour; NPs, nanoparticles.
Figure 7 Results of the study of average size of NPs in artificial saliva as a function of time. Abbreviations: ZnO, zinc oxide; Ag, silver; nm, nanometre; h, hour; NPs, nanoparticles.
Figure 8 Results of the study of average size of NPs in human saliva as a function of time. Abbreviations: ZnO, zinc oxide; Ag, silver; nm, nanometre; h, hour; NPs, nanoparticles.
Figures 6–8 present the change in the average size of the nanoparticles in deionised water, artificial saliva and human saliva, respectively. It must be underlined that these tests relate to the samples held in “dynamic conditions” and “static conditions.” This means that one part of the sample volume was stirred for the whole test duration (24 h) using the magnetic stirrer, while the remaining part was left to rest for over an hour in the silicone tubes and the measuring cell. Once an hour the whole volume was mixed together and a fresh sample portion was pumped into the measuring cell. The test conditions were similar to the conditions found in the oral cavity, i.e. e.g. a portion of the saliva is continually stirred while eating, while the remaining part, e.g. in the interdental area, remains static. The change in the average particle size in water (Figure 6, Tables S1–S5) was characterised by cyclic changes in average particle size. This means that there were several populations of various sizes of NPs agglomerates within the sample, which was caused by the varying speed of the suspension destabilisation processes in the dynamic and static states. The results for the ZnO+10%Ag suspension sample stand out particularly here. After 1 hr the average particle size had increased from approx. 600 nm to over 3000 nm, while after 12 hrs the average particle size decreased to below 500 nm. This means that the larger NPs agglomerates were sedimented and deposited in the silicone hoses supplying the “fresh” sample portions to the measuring cell, and that the suspension flow rate was too low to completely mix the deposited NPs agglomerates with the “fresh” portion of the suspension. Generally, based on the obtained results of the average particle size, it can be stated that the ZnO, ZnO+0.1%Ag, ZnO+1%Ag and ZnO+10%Ag samples underwent agglomeration and sedimentation processes during the test. Only the Ag NPs suspension sample displayed a steady growth in particle size without signs of cyclic changes in the results, which means that they were not deposited in the measurement system. It must be underlined that Ag NPs were the only ones that were modified and had a PVA coating, which considerably contributed to their suspension stability. For the samples of ZnO, ZnO+0.1%Ag, ZnO+1%Ag and Ag suspensions obtained in the artificial saliva (Figure 7, Tables S6–S10), an identical trend is visible, namely the average size increased from approx. 2000 nm (0h) to over 4000 nm (24h). Only ZnO+10%Ag NPs in the artificial saliva underwent a rapid agglomeration process, and already after the first hour of the test the average size was greater than 10,000 nm, ie greater than the maximum measuring range of the DLS analyser. In the case of the results obtained for human saliva (Figure 8, Tables S11–S15), after one hour of the test an identical trend was noticeable, i.e. a decrease in the particle size for the ZnO, ZnO+0.1%Ag, ZnO+10%Ag and Ag samples. A slight increase in the average particle size was observed only in the ZnO+1%Ag sample.
Figure 9 presents the stability profile of the sample of ZnO NPs suspension in human saliva. The remaining stability profile results are included in the supplementary files (Figures S1–S15). It must be borne in mind that the stability was measured in the “static” state, i.e. after closing the glass bottle, mixing and placing in the Turbiscan Lab analyser, the sample was not touched until the finish of the measurement process. Changes in the particle size and sedimentation were observed in each sample over the 24 hr analysis period (Figure 9, Figures S1–S15). The smallest changes in stability occurred for the suspensions of ZnO NPs, ZnO+0.1%Ag NPs, ZnO+1%Ag NPs and Ag NPs in deionised water. The largest change in stability profile was observed in the water suspension for ZnO+10%Ag NPs, in which both rapid sedimentation and rapid agglomeration of the NPs occurred.
Figure 9 Transmission profile of ZnO NP suspension in human saliva. Abbreviations: ZnO, zinc oxide; mm, millimetre; h, hour; m, minute; NPs, nanoparticles; T, transmission.
The collected stability profiles (Figures S1–S15) permitted calculation of the TSI parameter, which enables quick comparison and characterisation of the physical stability of the obtained suspensions. The higher the TSI value, the worse the stability of the sample. It is assumed that if the TSI value is the range 3->10, the destabilisation can be considered significant and may be noticeable to the naked eye, while if the TSI exceeds 10 the destabilisation can be considered as high and is certainly noticeable to the naked eye. Figures 10–12 summarise the results of the TSI parameter for the analyses carried out for 24 h. The lowest stability in all the media was recorded for ZnO+10%Ag NPs. The Ag NPs were the most stable NPs in deionised water and in artificial saliva, while the highest stability in human saliva was displayed by the ZnO+1%Ag NPs.
Figure 10 TSI values measured over 24 hrs for NP suspension in deionised water. Abbreviations: ZnO, zinc oxide; Ag, silver; NPs, nanoparticles; TSI, Turbiscan Stability Index.
Figure 11 TSI values measured over 24 hrs for NP suspension in artificial saliva. Abbreviations: ZnO, zinc oxide; Ag, silver; NPs, nanoparticles; TSI, Turbiscan Stability Index.
Figure 12 TSI values measured over 24 hrs for NP suspension in human saliva. Abbreviations: ZnO, zinc oxide; Ag, silver; NPs, nanoparticles; TSI, Turbiscan Stability Index.
In order to determine the causes of the different stabilities of NP suspensions in the two types of saliva, FT-IR analyses were performed. A representative FT-IR absorption spectrum of artificial saliva and human saliva sample is shown in Figure 13. The middle measurement range of infrared radiation (from 4000 cm−1 to 400 cm−1) was used, which is generally used for the qualitative analysis of lipids, proteins and carbohydrates. The characteristic bands of 3377 cm−1 and 3275 cm−1 were due to stretching vibrations of the N-H group of the protein amides. The two bands with maximums at 2918–2916 cm−1 and 2879–2872 cm−1 were due to symmetric and asymmetric stretching vibrations of the C-H group of the proteins and lipids. The spectral peak at 2052 cm−1 corresponded to the presence of thiocyanate (SCN−). Basic amide bands prevailed in the range from 1700 cm−1 to 1500 cm−1. The visible absorption bands within the range from 1700 cm−1 to 1600 cm−1 were due to stretching vibrations of the C=O group of the protein amides. The presence of the 1595 cm−1 and 1535 cm−1 bands was connected with the N–H bending vibrations of protein amides. The bands with wavenumbers of 1393 cm−1 and 1317 cm−1 were attributed to asymmetry and symmetry deformations of the protein methyl groups. The 1393 cm−1 band was probably also due to COO‑ stretching of ionised amino acid chains. The bands at 1317 cm−1 were due to bending vibrations of the C-H groups in α anomers, which were visible only in the artificial saliva samples. The absorption band present at 1054–1055 cm−1 was due to the different C–O stretching vibrations of the carbohydrate structure. The detailed comparative characteristic absorption values in cm− 1 for artificial saliva and human saliva are shown in Table 5.
Table 5 FT-IR Spectral Assignments For Samples Of Synthetic Saliva And Human Saliva
Figure 13 FT-IR spectra at RT of lyophilised samples of human saliva and artificial saliva. Abbreviations: FT-IR, Fourier Transform Infrared Spectroscopy; RT, room temperature; % – percentages.
Zinc oxide is commonly used as a material for temporary and permanent dental biomaterials due to the beneficial effect on the healing of the hard tissues of teeth and, to a certain extent, the antibacterial properties. Use of its nano-form was proposed to enhance its biocidal properties. However, nanosilver has recently been put into many dental devices in order to decrease the infection possibility. This study investigates issues related to the antibacterial activities of zinc oxide and silver nanoparticles against the bacteria responsible for odontogenic infections in the area of the head and neck, as well as their behaviour in the saliva. The release of H2O2 is a possible mechanism for the antibacterial activity of ZnO NPs,69 whereas the antibacterial activity of Ag NPs is based on cell lysis through the inhibition of DNA replication, expression of ribosomal and cellular proteins and interference with the electron transport chain.70
Kasraei et al71 showed that the addition of 1% of nanosilver or 1% of zinc oxide nanoparticles to a composite resin resulted in antibacterial properties against S. mutans and Lactobacillus Acidophilus. Moreover, they showed that zinc oxide NPs were significantly more effective against S. mutans than nanosilver. According to another study, Salem et al,70 zinc oxide nanoparticles inhibit adenylyl cyclase activity leading to the decade of the second messenger in the process of biofilm formation. In this study, biofilm formation was not evaluated, but the zinc oxide nanoparticles used as the sole antibacterial agent were significantly inferior to hydrosilver, which confirmed other observations that Zn NPs exhibited a relatively low antibacterial capacity.72,73 The addition of either 0.1%, 1% or 10% of silver to Zn NPs significantly increased their antibacterial capacity against all the investigated species. Interestingly, this effect was not related to the percentage of Ag added. The MIC values decreased threefold (from 125 ppm up to 32 ppm) when silver was used as a compound (Supplementary materials). Observations taken from microbiological studies confirmed the high antimicrobial potential of nanosilver and its compounds against bacteria that are commonly responsible for odontogenic infections of the head and neck, described in prior research.11,74 Indeed, when properly applied, NPs may find a real application as an antibacterial agent able to reduce the spread of MDR species and reduce the incidence rate of nosocomial infections. As NPs and their ions released from metallic materials may provide a high antibacterial activity in the peri-implant space, such materials are expected to be applicable as drug containing implants used in sites at greater risk of infection development.75
Nevertheless, it is well known that nanoparticles with high antimicrobial properties may also exert a toxic effect on the host’s tissues due to reactivity and mostly through reactive oxygen species (ROS) formation. Therefore, the therapeutic window for each nanoparticle-eluting biomaterial should be evaluated first. It may be calculated only when the biological interactions of NPs in the specific environment are taken into account. Each tissue and organ has its unique microenvironment composed of proteins, sugars, micro- and macroelements, which provide homeostasis when balanced. The introduction of NPs into this environment may exert an impact on this homeostasis and contribute to an unpredictable reaction on the part of the living organism, such as inflammatory response, irritation, rash or even carcinogenic effect when exposure is prolonged. Therefore, any biological reaction of the human body to a chemical agent that is not fully profiled must be taken into account. Nanoparticles, when detached from the material’s surface, are suspended in the biological fluids and interact with its compounds, changing their conformation, reactivity and physicochemical properties. The complexes formed by NPs with proteins and sugars are described as protein coronas (PCs). As PCs travel through the body, interactions with different molecules occur and the coronas may dissolve, form conglomerates or even new compounds with unique properties. This process is known as “from synthetic to biological identity” and describes changes from the NPs properties designed in the laboratory to those gained by their interaction with a specific biological environment. This means that any NPs exposed to the body may form biological medium-related, unique coronas, which exert some impact on both antibacterial and toxicological activities. Several studies have attempted to elucidate these complex phenomena, but the vast majority of the studies focused on interactions between nanoparticles and blood plasma.76–78 Several factors play a role in the whole interaction process between NPs and protein-rich biological fluids. Lundqvist et al.12 showed that the size of the NPs influenced this process due to the curvature effect in human blood serum. They proved this in a study where silica nanoparticles of the same type but of various sizes differently influenced the binding of A-lipoprotein from human blood. The smaller the NPs, the greater the number of proteins that bound as PCs. Also, they showed that the bigger the NP size, the more up-regulated the thrombin-generation assay. The authors, therefore, showed that the same NPs, but of various sizes, may affect the organism response in different ways. Also, Ajdar et al.76 showed that gold nanoparticles added to human blood generated a faster prothrombotic response (in a nonlinear size dependent manner). They also showed the concentration dependent manner of the prothrombogenic effects and reduction of time until initial clot formation. Moreover, they noticed that clot strength decreased significantly in line with the size of the NPs added.76
The aforementioned studies confirmed the extreme diversification of the interactions between NPs and biological fluids. Few studies have yet evaluated PC formation in the oral cavity, or sufficiently explained their impact on the oral mucosa and its permeability.3 Moreover, the results obtained in human blood serum or whole blood models cannot be transferred straightforward to the saliva, as it is a hypotonic fluid with low ionic strength, containing calcium, phosphate, carbonate, thiocyanate ions, proteins and mucin, which ensure its gel-like structure and viscoelastic properties. Moreover, approximately 73% of the salivary proteins are not present in the plasma, which implies a necessity for meticulous studies on this interaction model, especially as the oral cavity is a significant administration route for NPs. Therefore, an attempt to profile the PCs formed in the human saliva by two of the most widely used nanoparticles: silver and zinc oxide, was made in this study, because to the authors’ best knowledge it was a crucial step towards a better understanding of the real potentials and limitations of nanodentistry and its current approaches.79,80 As nanoparticles introduced into the body via oral route will interact with the saliva and its molecules, PCs of distinct conformation and physicochemical properties depending on nanoparticle type are expected to occur. Such PCs may exert different effects on the tissues of the oral cavity, including the lining mucosa, gingiva, teeth and others, leading to unexpected local outcomes. NPs may penetrate the oral mucosa and travel throughout the body by the passive diffusion, blood circulatory or lymphatic systems, be deposited in the organs, penetrate cell membranes, accumulate in the mitochondria, and trigger injurious responses.81 Otherwise, materials containing NPs and placed beneath the tissues may adversely affect them.
It was shown that the morphology of nanoparticles exposed to saliva or any other biological fluids may change, depending on the fluid’s pH and composition. In the presence of a biological fluid characterised by a neutral pH and high ionic strength, NPs may immediately start to aggregate and continue this process over a prolonged contact period, caused by the diminishing electrostatic repulsion between NPs and hydrophobic interactions.82,83 Differences in affinity to agglomeration between different NPs are caused by the ionic strength level of the medium and the nanoparticles properties per se, such as size, distribution, shape, crystal structure, chemical composition, surface area, functional groups, charge or porosity and stabilisers.83 Depending on the NPs charge and stability gained in silico, the nanoparticles may be unstable in the presence of proteins or even precipitate to macroscopically detected agglomerates.83 Such agglomerates may significantly mediate the cellular responses, cell uptake and the mechanism of endocytosis, biodistribution, circulation duration, clearance and permeation of the oral mucosa.82 In the study by Halamoda-Kenzaoui et al.84 the agglomeration level of NPs contributed to increased cellular uptake and modified endocytosis mechanisms. Dispersed 80 nm particles were more likely to be up-taken by cells through caveolae-mediated endocytosis, whereas those sized 30 nm entered the cells via a combination of different endocytic pathways such as clathrin-mediated endocytosis and micropinocytosis.84
In the work by Teubl et al13 and Teubl et al85 in turn, the cellular uptake capacity of NPs after incubation in saliva was half that of a serum-free medium. Also, functionalised, positively and uncharged particles interacted to a greater extent with the salivary components than uncharged NPs.13,85,86 In a study by Walczak et al87 the sizes of the Ag NPs were stable during the 24 h of incubation in artificial saliva. They explained that media containing proteins may stabilise how the particles and silver nanoparticles agglomerate to a greater extent in fluids with a higher ionic strength than saliva.87 Pindakova et al82 noticed, however, that the presence of artificial saliva induced the growth of Ag NPs from 90±2 nm immediately after mixing to 248±8, measured after 180 mins in contact with the medium. Regardless of the agglomeration process, they did not observe any cytotoxic effect of the nanosilver agglomerates in reconstructed oral cavity cell lines. Moreover, Ag NPs were reported to down-regulate the production of inflammatory cytokine IL-1α and, therefore, show anti-inflammatory properties. This is promising as nanosilver has recently been proposed as an additive to titanium oral implants in order to decrease peri-implant infections and other biomaterials used in the reconstruction of teeth and the craniofacial area.11 Discrepancies between studies show that the presence of certain proteins in the medium may induce, slow down or prevent agglomeration and imply diverse effects on the cellular uptake of NPs in different individuals.
In this study, agglomeration by all NPs in the tested media was observed. However, when exposed to artificial saliva, the NPs formed complexes that were significantly larger than their counterparts incubated in deionised water. Saliva is a highly complex biological fluid composed of water, proteins, enzymes, hormones, ions, products of the enzymatic decomposition of carbohydrates, leukocytes, bacteria and flaked-off cells of the oral cavity epithelium.88–92 It must be underlined that human saliva is characterised by a unique composition, which depends on such factors as age, gender, stress, health condition, physical effort and type of stimulants consumed (e.g. tobacco).58,59,66,92 Teubl et al13 proved that saliva was characterised by a porous structure, where the pore size ranged from ≈200 nm to ≈2000 nm, while the pores were filled by a fluid of low viscosity. The critical factors influencing the agglomeration and stability of the NPs are nanoparticle type and fluid type (Table 4). It is not surprising that the NPs (apart from ZnO+10%Ag NPs) displayed the lowest agglomeration and highest stability in deionised water, which featured a low content of ions and an absence of macroparticles. The low quantity of the ions in the suspension causes a broadening of the diffuse layer of ions in the “electrical double layer” surrounding the NPs, which as a consequence results in increasing the range of the electrostatic energy of repulsion.93 In other words, in the case of a low specific conductance (low ionic strengths), the electrical double layer is dispersed, thanks to which it extends “far” from the particle surface, which increases the effectiveness of the particle–particle repulsions. The lack of electrostatic stabilisation (ζ=0.5 mV) and the large size of the aggregates of ZnO+10%Ag NPs (approx. 500 nm) explain the speed of the ZnO+10%Ag NPs sample sedimentation in deionised water. It is common knowledge that the higher the size of NP agglomerates/aggregates, the quicker the process of their sedimentation. Thanks to the surface modification with PVA, Ag NPs are distinguished by stability and a lack of significant changes in their average size in deionised water, even after the elapse of 24 h. The modification of the NP specific surface with various polymers is a key strategy in obtaining stable suspensions (steric stabilisation),94 while the hydrophilic properties of polymers contribute to the emergence of additional stabilisation through the short-range repulsive hydration forces.95
A rapid increase in the average particle size (Table 4) and particle sedimentation (Figures S6–S10) were observed in all NPs suspensions obtained in artificial saliva. Similar results were obtained by Reubl et al13 in that they proved that from among all the media used in the tests, NPs underwent the quickest agglomeration in saliva. There are two explanations for this phenomenon. The first is that high ionic strengths result in the compression and neutralisation of the diffuse layer in the electrical double layer of NPs, thanks to which the van der Waals forces cause the agglomeration of NPs.96,97 The multivalent counterions present in saliva, e.g. HPO42−, CO32−, SO42− ions, may quickly interact with the cations (or the other way round) in the adsorption layer of NPs, at the moment they are introduced to the saliva. This causes a change in the ionic composition of the electrical double layer and screening of the surface charge, which is explained by the strong interactions between the ions and counterions. The second explanation is the formation of the protein corona around NPs and their agglomerates, and the formation of hydrogen bonds between the protein corona and the particles, proteins and other various molecules. The formation of large nanoparticle-protein aggregates can trap proteins that do not adsorb to the nanoparticle surface, i.e. they are not part of the corona.12 Both the interactions of the mono- and multivalent salivary ions with the electrical double layer on the surface of nanoparticles and the formation of protein coronas contribute to the agglomeration of NPs in artificial saliva, which was visible throughout the whole test duration (24h). An interesting correlation was noticeable for nanoparticles suspensions in artificial saliva: namely, the average particle size increased in line with the increase in Ag NPs content in the ZnO+x·Ag NPs samples (Figure 7). It is likely that this correlation can be explained by the different formation of a protein corona around the particles.87 This correlation shows that Ag NPs without surface modification display no stability in the saliva whatsoever, which was indicated by the rapid agglomeration of the ZnO+10%Ag sample (>8000 nm), characterised by the highest Ag NPs content.
It must be pointed out that the size, morphology and degree of agglomeration of the ZnO+x·Ag NPs samples depend on the silver content (Figure 2). This results from the impact of the presence of Ag NPs on the course of the synthesis of ZnO NPs. Ag NPs are formed earlier than ZnO NPs, which is a consequence of the different mechanisms of reaction. Ag NPs are formed in a single-stage reaction of reduction of Ag+ to metallic Ag°, while ZnO NPs are formed in a reaction where two primary stages can be distinguished.36 Namely, the formation and growth of the intermediate (Zn5(OH)8(CH3COO)2·xH2O) and the rapid decomposition of the intermediate to ZnO NPs, and the growth thereof until the zinc acetate is used up. The Ag NPs formed earlier disturb the decomposition of the intermediate into individual ZnO NPs, and this is why SEM photographs show how aggregate size increases in line with increase in the Ag NPs content in the samples; this is particularly noticeable for the ZnO+10%Ag sample. We observed a similar impact on the morphology and size of the microwave synthesis products when the dopant content in ZnO NPs increased.98,99 Obviously, one should bear in mind that the degrees of agglomeration could alter the particle degradation and circulation kinetics.
The visible change in the zeta potential by as much as 107 mV for ZnO NPs in the artificial saliva relative to the ZnO NPs suspension in deionised water results from the formation of a new electrostatic equilibrium of the electrical double layer (Table 4). Despite the theoretical electrostatic stability arising from the zeta potential value exceeding |30 mV|, the NPs samples displayed a lack of stability (agglomeration, sedimentation). The results obtained in these tests prove that a zeta potential value exceeding |30 mV| does not guarantee stability in biological fluid suspensions, which is caused mainly by the formation of the protein corona on NPs. The protein corona fulfils two primary functions: NPs destabilisation and surface inertisation. It is saliva that is the first protective mechanism of the human organism, which is supposed to reduce the activity of the NPssurface and to prevent penetration of NPs through the cell membrane in the oral cavity. Moreover, if NPs penetrate into the human organism, the protein coronas may significantly reduce their circulatory life span in the blood.100
Very interesting results were achieved for NPs suspensions in the human saliva. The transmission profiles of NPs in the artificial saliva (Figures S10–S15) showed that over the 24 h period the NPs underwent agglomeration and sedimentation. After 1 hr of analyses by the DLS method, in turn, the average size of the NPs in the human saliva did not change significantly (Tables S11–S15, Figure 8). The differences in the results of suspension stability can be explained by the different manner of sample preparation before the analyser measurements. The Turbiscan Lab analyser recorded the changes in particle size and sedimentation of NPs in the suspension sample being in the static state in the measurement cell, while the DLS analyser collected a “fresh” portion of the sample every hour, which was stirred over the whole test duration using the magnetic stirrer. The results indicate that in human saliva the NPs agglomeration process features weaker forces53 and is reversible through mechanical stirring of the suspension. In comparing the composition of human saliva to the composition of artificial saliva, two primary differences are visible (Figure 13). Namely, SCN− anions were present only in the human saliva sample and the quantity of carbohydrates was considerably lower than in the artificial saliva sample. It is probable that SCN− anions were rapidly adsorbed on the surface of the NPs, in particular of the Ag particles, which might have limited or prevented permanent coating of their surface with the protein corona. The presence of thiocyanate (SCN-) anions in the saliva is quite unique. In saliva, SCN− is converted by salivary peroxidases to hypothiocyanite (OSCN-), a local antibacterial agent with high efficiency.101 It was proved that the content of thiocyanate (SCN-) anions was closely related with smoking among the participants in earlier tests,102 which indicated that some of the saliva donors were smokers.
In comparing successive and very significant saliva parameters, i.e. pH and specific conductance, considerable differences between artificial saliva and human saliva are noticeable (Table 4). As saliva samples were used from different patients, parameters such as ionic strength and pH could vary depending on complex interactions between the different saliva components, which give rise to the different properties of the PCs.103 Therefore, the results obtained may differ from the analytical data (artificial saliva used within this study). The literature reports105–107 that the pH value of human saliva depends on the stimulation process and ranges from 5.3 to 7.8. The high pH (7.84±0.07) obtained for the human saliva sample could be attributed to a difference in the composition of electrolytes, including a greater bicarbonate concentration, which would also explain the high specific conductance (4361±6 µS/cm). The differences in the zeta potential results can be explained mainly by the different pH and specific conductance values. It is also quite surprising that, despite the higher specific conductance and hence the greater electric field screening for human saliva, the NPs underwent slower destabilisation processes than in artificial saliva. This indicates that the protein corona of NPs that formed around the NPs in the human saliva contributed to the limitation of the destabilisation processes, hence to the improvement of their stability. Based on the results it can be stated that NPs in human saliva might maintain a relative stability while chewing, despite a zeta potential value below |30 mV|, probably thanks to the presence of certain metabolic products and organism detoxication products, e.g. (SCN-).
Nanoparticles can penetrate into the oral cavity in several ways, e.g. as solid air pollution, as an ingredient of a medicinal product (e.g. for oral cavity rinsing) and in the form of modification of a tooth implant surface. Prolonged and repeated exposure of the oral tissues to nanoparticles may result in cumulative effects. This process is related to the exposure rate, tissue type and fluid used.82 The permeation process may be up- or down-regulated by specific enzymes. The agglomeration of NPs in the biological fluids may, however, decrease toxicity, as was shown in the study by Zook et al.108 The acidic pH of the fluids decreases the agglomeration of NPs with proteins, whereas alkaline pH up-regulates this process. In the presence of proteins in the intestinal digestion model, NPs may form complexes composed of silver, sulphur and chlorine.87 Therefore, they may aggregate and disperse as they travel throughout the body, constantly changing their properties.82,87 Also, the composition of PCs is strongly related to the competition between the proteins present in the medium to be adsorbed on the NPs surface. Protein affinity to agglomeration is also related to pH, NPs charge, particle-protein interaction and protein identity.109 PCs may both exhibit a toxic effect or increase the biocompatibility of NPs due to conformational changes of the proteins and the agglomeration of NPs. Specific PCs and their impact on certain tissues are still unknown.
Nanoparticles of zinc oxide and silver form a significant group of nanomaterials characterised by antibacterial properties, which have recently begun to be widely applied in medicine. The continually growing number of new applications of ZnO NPs and Ag NPs, e.g. in the modification of dentures or of implant surfaces, and consequently the continuous contact of the organism with these NPs might have a potential impact on human health. Therefore, it is necessary to acquire important information about the behaviour of ZnO NPs and Ag NPs in biological fluid, namely saliva, which faithfully reflects the oral cavity environment.
Ag NPs, ZnO NPs and three mixtures of ZnO+x·Ag NPs were used in the tests. ZnO+x·Ag NPs samples were obtained thanks to the unique method of microwave solvothermal co-synthesis, which is presented for the first time. ZnO NPs and mixtures of ZnO+x·Ag NPs were characterised by an average size of 30±3 nm and a spherical shape. The actual composition of the ZnO+0.1%Ag NP, ZnO+1%Ag NP and ZnO+10%Ag NP mixtures was as follows: ZnO+0.00042·Ag NPs, ZnO+0.00516·Ag NPs and ZnO+0.0446·Ag NPs.
Colloidal Ag NPs were most efficient in eradicating all the tested oral bacteria. The presence of small quantities of Ag NPs in the ZnO+x·Ag NPs mixture almost doubled its antibacterial potential. Nanoparticles based on ZnO NPs or its compounds without Ag NPs exhibited a significantly inferior antibacterial potential when compared to Ag NPs.
The static multiple light scattering analyses indicated that all NPs suspensions, both in human saliva and in artificial saliva, underwent sedimentation and agglomeration processes over the whole test duration. Such factors as saliva composition, ZnO+x·Ag NPs mixture composition and NP type all affected the kinetics of suspension destabilisation. The ZnO+0.0446·Ag NPs sample had the highest content of unmodified Ag NPs and displayed the fastest destabilisation kinetics in all the fluids used.
The dynamic light scattering analyses indicated a rapid agglomeration process for all NPs samples at the moment they were introduced to artificial saliva. The average size of all NPs in artificial saliva gradually increased over the whole duration of the tests. The process of NPs agglomeration in artificial saliva was mainly related to the formation of the protein corona that coated the NPs surface.
The tests of the average particle size in human saliva showed that the process of NPs agglomeration in this biological medium was reversible as a result of mechanical stirring.
This study was conducted in accordance with the Declaration of Helsinki. All patients received and signed the written informed consent, and the study was approved by the Warsaw Medical University Ethical Committee, no. KB/150/2018.
This project has been supported by AOCMF, Project AOCMFS-18-14P. A part of the research was carried out with the use of equipment funded by the CePT Project, reference: POIG.02.02.00-14-024/08, financed by the European Regional Development Fund within the Operational Programme “Innovative Economy” for 2007–2013. This work is partially supported by the National Center for Research and Development (NCBR), Poland, project iTE (STRATEGMED3/306888/3/NCBR/2017). The authors would like to thank Stanisław Gierlotka and Jan Mizeracki (Institute of High Pressure Physics of the Polish Academy of Sciences, Warsaw, Poland), and Roman Mukhovskyi. The authors would also like to thank Andrzej Stanisz, MSc (Department of Bioinformatic and Telemedicine, Jagiellonian University Medical College, Krakow, Poland) for statistical analysis of the obtained data.
The authors report no conflicts of interest in this work.
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