On-Site Surface Functionalization for Titanium Dental Implant with Nanotopography: Review and Outlook

Kim, Byung Gyu; Seo, Seog-Jin; Lee, Jung-Hwan; Kim, Hae-Won

doi:https://doi.org/10.1155/2016/3429532

Journal of Nanomaterials

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Advances in Functionalized Materials Research 2016

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Review Article | Open Access

Volume 2016 | Article ID 3429532 | https://doi.org/10.1155/2016/3429532

On-Site Surface Functionalization for Titanium Dental Implant with Nanotopography: Review and Outlook

Byung Gyu Kim,¹Seog-Jin Seo,^2,3Jung-Hwan Lee ,^1,2and Hae-Won Kim^2,3,4

Academic Editor: Régis Guegan

Received22 Apr 2016

Accepted04 Sept 2016

Published25 Sept 2016

Abstract

Titanium (Ti) has been the first choice of material for dental implant due to bonding ability to natural bone and great biocompatibility. Various types of surface roughness modification in nanoscale have been made as promising strategy for accelerating osseointegration of Ti dental implant. To have synergetic effect with nanotopography oriented favors in cell attachment, on-site surface functionalization with reproducibility of nanotopography is introduced as next strategy to further enhance cellular bioactivity. Extensive research has been conducted to investigate the potential of nanotopography preserved on-site surface functionalization for Ti dental implant. This review will discuss nonthermal atmospheric pressure plasma, ultraviolet, and low level of laser therapy on Ti dental implant with nanotopography as next generation of surface functionalization due to its abilities to induce superhydrophilicity or biofunctionality without change of nanotopography.

1. Introduction

Titanium (Ti) has long been used as an implant material in dentistry due to its remarkable corrosion resistance of its Ti oxide layer and powerful physical load [1]. In order to improve biological functions of Ti implants, various techniques of Ti surface modification such as surface roughness, chemistry, topography, and electrical charge have been suggested, focusing on the biological performance of Ti surface properties [2]. These surface modifications at the micrometer or nanometer scale have effectively promoted biological performance of Ti implants such as cell growth and functions in vitro [3, 4] and osseointegration in vivo [5] when compared to untreated surfaces.

Recently, nanostructures of Ti implant surface have been shown to further mimic the natural bone structure, possibly considering the biological pertinence of nanotopography for osteoblast or stem cells to attach, proliferate, or differentiate to achieve osseointegration [6–8]. For this, various methods for surface nanotopography of Ti implants have been developed at the nanoscale, such as lithography [9], crystal deposition [10], acid etching [11], sandblasting [12], and their combinations [13, 14]. Although these techniques physically or chemically are known to obtain optimal surface characteristics for accelerating osseointegration in the field of basic research, reactivating surface functionality on aged Ti implants may be issued in a clinical setting, probably leading to clinical failure in dental implants [15]. In addition, rough Ti surfaces are generally hydrophobic and have high tendency to bacteria attachment, which can cause high risks of peri-implantitis, consequently failing in dental implant cases [16, 17].

To overcome these, several nanotopography preserved on-site surface functionalizations for Ti implants have been suggested: nonthermal atmospheric pressure plasma, ultraviolet, and laser [18–21]. On-site surface functionalizations are one of the alternative strategies to existing surface modifications and can maintain nanotopographical surfaces of Ti implants due to the chair-side applicability, sustainability of functionalized effects with their enhanced biological potential before implant surgery, and no-damaged surface roughness. This review covers and suggests possible on-site applicable surface functionalization methods for Ti dental implant (Figure 1).

2. Nonthermal Atmospheric Pressure Plasma

Plasmas are defined as “the 4th state of matter” and contain a large amount of highly reactive species including ions, free radicals, electrons, and electronically excited atom or neutrals [22]. When plasma is produced at atmospheric pressure and the temperature of excited gas is at 300 K around, nonthermal atmospheric pressure plasma (NTAPP) is produced and can be treated onto the surface of implants for functionalization by the controllable plasma reactive species [23].

Once being exposed to plasma, the surface properties of the biomaterials can be functionalized as a result of the “bombing” of these reactive species. NTAPP treatment on biomaterials has been used to improve surface properties and to induce decontamination [24]. Because NTAPP has several advantages, such as induction of an increase in surface energy with very short treatment time, being on-site applicable, preservation of nanotopography, relatively low price, and simple fabrication process compared to vacuum-based plasma [25], NTAPP treatment has gained attention for Ti dental implant functionalization with preserving nanotopography [26, 27]. For instance, cell size of human osteoblastic cells adherent on argon-based-NTAPP-pretreated specimen was significantly larger than that on nontreated surfaces irrespective of surface topography, which supported spreading of osteoblastic cells and thereby could accelerate osseointegration [28]. In terms of osteoblastic-differentiated gene expression, Nitrogen or air-based NTAPP-treated TiO₂ nanotubes exhibited higher osteogenic gene expressions level depending on the working gas without changes in nanotopographical morphology [29].

In an additional example, nitrogen-based NTAPP-treated sandblasting with large-grit sand particles and acid etching subsequently (SLA) treated dental implant, which is clinically accepted golden Ti surface with microtopography/nanotopography, improved cellular activity on treated surface as well as wettability. Preosteoblast attachment and its proliferation were increasingly observed on NTAPP-treated SLA dental implant due to increased wettability and decreased hydrocarbon contamination without topographical changes. Both studies opened the possibility of application for enhancing osseointegration of Ti dental implants in a way of nanotopography preserved state [27].

Additionally, NTAPP treatment can be applied for increasing success of Ti dental implant by increasing soft tissue healing and preventing peri-implantitis. Human keratinocytes and HGFs on NTAPP-treated Ti implants showed an increase in proliferation or migration, which is beneficial for increasing implant-soft tissue sealing [30]. Additionally, direct NTAPP treatment to adherent human gingival fibroblasts (HGFs) on machined Ti substrates revealed possible application for gingival tissue healing due to an increase in intracellular reactive oxygen species (ROS) and upregulation of three migration-related genes (EGFR, PAK1, and MAPK1) and EGFR activation [21]. Recently, NTAPP treatment onto Ti dental implants has shown antifouling effects to oral bacteria related to peri-implantitis. Roughened Ti surfaces including SLA have hydrophobic characteristics, leading to inducing bacteria attachment and consequently failing in implants. Investigation of the effects by NTAPP treatment on the Ti dental implant surfaces for the inhibition of two common pathogens (Streptococcus mutans and Staphylococcus aureus) was carried out and showed that there was a reduction of adherent bacteria and the significant change in morphology of bacteria. These results were attributed to increased hydrophilicity on the surface of NTAPP-treated Ti implants [20].

NTAPP has been applied for enhancing success of dental implant restoration with sustaining topographical characteristics in the nanoscale, but there are still limitations in terms of clinical application. NTAPP-produced radicals, which play a major role to modify surface characteristics, are easily influenced by even tiny change in humidity and gas composition, which do not guarantee reproducibility of NTAPP equipment in clinical situation. Moreover, safety issues from exposed radicals to air could be raised because they can react with sensitive normal tissues such as eyes. With regard to prevention of possible exposure to eye and other exposed tissues, high volume suction should be accompanied to evacuate any radical plume created during plasma production, and protective eyewear should be worn for operator, patients, and other assistant people. In terms of osseointegration by NTAPP treatment, in vivo or preclinical study has not been performed to show possibility of clinical application. For overcoming above limitations, accurate NTAPP machine with controlled working gas injector is needed to set up reproducibility of NTAPP-induced radical, and in vivo study using rabbit or adult dog to investigate osseointegration is necessary.

3. Ultraviolet

Ultraviolet (UV) photofunctionalization to Ti implants can alter physicochemical properties of the surface, such as generation of superhydrophilicity and pollutant-degrading, antifogging, antibacterial, and stain-proofing properties [31, 32]. Enhancement of biologic capabilities without topographical change was able to be observed on the surface of UV-treated TiO₂ semiconductor [33].

In terms of biologic ability from UV treatment, bone morphogenesis around UV-treated Ti implants was distinctly improved compared with untreated control implants, leading to rapid and complete establishment of osseointegration with nearly 100% bone-to-implant contact in an animal model, as opposed to less than 55% for untreated implants [33]. A series of in vitro studies demonstrated considerable enhancement of attachment, proliferation, differentiation, and subsequent functional cascades of osteogenic lineages from animals and humans after UV treatment [34]. Basically, UV treatment is known to convert Ti surfaces from hydrophobic to superhydrophilic due to removal of unavoidably contaminated hydrocarbons [35]. In this model, UV treatment creates more expression of Ti⁴⁺ sites on outer Ti surface, which is favorable for dissociative water or adhesive protein adsorption. In addition, UV-treated Ti surfaces manifest a unique electrostatic status and thereby act as direct cell attractants without the help of ionic and organic bridges, which induces a novel physicochemical functionality to Ti [36]. Other advantages of UV treatment are simplicity of treatment devices and treatment methods, low cost, portability, and diverse applicability for all types of Ti alloys (Ti6Al4V and Ti-Ag) and Ti surfaces tested such as machined surfaces, SLA, and Ti nanotube formed and micro-arc oxidation surface [37–40].

When SLA surface, most promising Ti surface among commercially available dental implants, including nanopits and micropits was treated by UV, it induced superhydrophilicity, tailored mesenchymal stem cells into osteoblastic lineage, and accelerated attachment, proliferation, and migration without change of surface architectures [36, 41]. The attachment, spreading, settling, proliferation, and alkaline phosphate activity of bone marrow-derived osteoblasts were promoted on Ti or apatite-coated Ti after photofunctionalization compared to nontreated counterpart, which induced high bone-implant contact to reduce peri-implant stress [42]. Most of the upregulated biofuctionalities by UV photofunctionalization were revealed due to an increase in protein adsorption such as fibrinogen and other attachable proteins [43].

UV-mediated photofunctionalization is effective to enhance bone tissue formation on the Ti mesh [44]. In addition, UV photofunctionalization accelerated and enhanced levels of osseointegration and overcame impaired osseointegration even in type 2 diabetes using a rat model [45]. In a clinical study, implant stability and osseointegration speed of immediately loaded implants were increased through UV treatment. Additionally, UV irradiation reduced the attachment and biofilm formation of wound pathogens on various topographical Ti surfaces [46]. The mechanism might involve superhydrophilicity and carbon elimination on the surface. These data suggest that UV photofunctionalization can be a novel, effective measurement to improve implant therapy for mal-regenerative patients in the dental and orthopedic fields. Besides, UV treatment is able to overcome time-related degrading bioactivity of Ti, which means UV on-site treatment on Ti has a potential to restore the possible adverse effects of Ti aging in terms of osseointegration [35, 47]. From manufacturer, UV-pretreated dental Ti including SLA-treated Ti has been distributed in market with being immersed into CaCl₂ and NaCl₂ solution to avoid Ti aging. However, future research will be needed to validate these promising aspects using in vivo or clinical studies in terms of enhanced osteoconductivity [34].

Even though UV treatment has been applied for enhancing success of dental implant restoration without change of topographical characteristics, there are still limitations in clinical applications. UV treatment requires relatively long exposure time compared to NTAPP and thereby cannot apply for on-site treatment in clinical situation. Whether specific type of dental implants is set to be exposed to UV treatment according to the anatomical data from digital images, they can be changed into another type depending on the bone width, height, and density on surgery day for Ti implantation. Moreover, safety issues from photofunctionalized Ti surface could be raised because the surface can react with stem cells and may activate various biological signaling in an unexpected way, which can adversely affect osseointegration. In addition, interplay with osteoclast, macrophage, and other important cell types for osseointegration is still under investigation. Even though, in terms of osseointegration by UV treatment, in vitro, in vivo, or preclinical study has been performed to show possibility of clinical application, biological mechanisms of cells on photofunctionalized Ti surface and safety issues are still remaining under consideration. For overcoming above limitations, UV machine with high performance is needed to be developed for decreasing treatment time for on-site application of nanotopographical Ti implants and more in vitro studies for revealing cellular mechanisms and long term in vivo or clinical studies are necessary to investigate promising and safety usages of UV treatment for successful osseointegration.

4. Low-Level Laser Therapy

The term “laser,” which is an abbreviation for “Light Amplification by the Stimulated Emission of Radiation” was firstly applied in dentistry by Maiman in 1960 and has been used for hard and soft tissue applications especially for removing or cutting certain part of them [48]. For example, in hard tissue application, the laser is used for cutting bone, bleaching, restorative removal, and cavity preparation as well as caries prevention and dentinal hypersensitivity, whereas soft tissue application includes removal of soft tissue to uncover impacted or partially erupted tooth or photostimulate herpetic lesion or malignancies [49]. In the United States, the use of lasers was first approved by the Food and Drug Administration in around 1990s on the gingival soft tissue, and use on hard tissue such as teeth or the bone of the mandible gained approval in 1996 [50]. In the last decade, there has been an explosion of research investigations in laser application on Ti implant surface due to many advantages of laser such as great specificity, on-site applicability with currently used laser device, and cost-efficiency [51].

Several variants of dental lasers are in use with different wavelengths and these mean they are better optimized for different applications. There are two types: on one hand there are hard lasers such as Er:YAG laser and Er,Cr:YSGG laser, whereas, on the other hand as cold or soft laser, there are carbon dioxide lasers, Nd:YAG laser, and light-emitting diodes, which are compact, low-cost devices, and they are termed as low-level laser therapy (LLLT) or “biostimulation” [52]. Hard lasers and other soft lasers except LLLT have limitation in applying for nanotopography preserved on-site surface functionalization for Ti dental implants due to surface roughness changes as well as high costs [53]. Even though above laser-treated surfaces induced an increase in biologic response with bone marrow stem cells and many types of osteoblastic lineages and may lead to improved bone-to-implant contact due to high surface energy and the macrostructures/microstructures of Ti implant [54, 55], topographical characteristics could not be preserved in nanoscale. Therefore, LLLT pretreatment on Ti dental implants and its effects for osseointegration will be discussed in this section.

LLLT including diode laser, gallium-aluminum-arsenide (GaAlAs) diode, and helium-neon laser have been introduced to have biostimulating potentials on Ti without surface morphology changes, therefore accelerating the healing process [56]. The area of effect is larger than that in the high-energy hard laser ones and therefore the heat is dispersed well, which may not result in alterations of the surface topography in the nanoscale. Therefore, most studies with LLLT in implantology were focused on an acceleration of osseointegration on Ti implants. There exist many articles analyzing the potential effects of these therapies on the osseointegration of Ti dental implants. The results in the group irradiated with LLLT on Ti implants reported beneficial effects from the microscopic point of view: increased bone-implant contact, better bonding ability to natural bone, greater percentage of calcium, phosphates, and hydroxyapatite composition in healing site, an increase in osteoblast differentiation related gene expression such as osteoprotegerin, receptor activator of nuclear factor kappa-B ligand, and no effect on bone resorption [57–62]. Above in vitro data suggest that LLLT irradiated Ti has a potential to induce faster bone maturation, improves bone healing, and increases the cellular activity, including proliferation and attachment, in Ti material with increased activity of alkaline phosphatase compared to the control group [62].

Besides, the use of LLLT can be applied for treating chronic periodontitis, hypersensitivity, oral mucositis, and orthodontic pain as well as decreasing infections around dental implants [63–66].

Even though LLLT treatment has been applied for dental implant restoration without change of topographical characteristics, there are still limitations for clinical application. LLLT treatment also requires more than 24 hours, which is relatively long exposure time compared to NTAPP and cannot be applied for on-site treatment in clinical situation. Even though a specific type of dental implant is exposed to LLLT treatment in clinic, dimensions of Ti implant can be changed. Although optimized time of LLLT did not induce changes in topology, there is still a chance of alteration in the nanoscale when treatment time is increasing. In addition, in terms of rationale to link LLLT-treated Ti and osteoblastic lineage, there is insufficient proof at the moment. Safety issues from LLLT treatment also remain because certain precautions should be taken to ensure safety [49]. First and foremost risk factor is eye damage from laser to anyone such as operating doctor, assistants, and patient during procedure. It should be advised to wear protective eyewear for preventing potential eye damage. Additionally, accidental exposure to nontarget biomaterial or normal tissues such as surrounding tissue or finger of operator can be prevented by the use of protective ware and limiting access to the equipment and operating environment to minimize the unwanted effects from reflective laser. In terms of osseointegration by LLLT treatment, more in vitro, in vivo, or preclinical studies are necessary to show possibility of clinical application and to optimize protocol (power, time, and type) to induce increase of biological activity of osteoblastic lineages without topographical changes because only few in vitro and animal studies have shown a positive effect on osseointegration of Ti implants.

5. Concluding Remarks

Table 1 shows advantages and disadvantages of on-site surface functionalization method for Ti dental implant. Among three potential nanotopography preserved functionalizing methods, NTAPP seems to be the best due to short treatment time and high efficiency to induce superhydrophilicity. UV treatment mostly used in clinics is also convenient except long period for treatment, which is the reason why UV treatment is only performed in manufacturer. With the drawback in terms of long treatment time, LLLT treatment using various types of lasers has the longest history and may be acceptable due to its early introduction to dental application for modifying surface characteristics on Ti surface. However, it is still unclear to understand biological mechanisms to link the bridge between LLLT-treated Ti and cells as well as clinical study.

On-site surface functionalization is considered as a promising strategy to enhance osseointegration due to synergetic advantages from reproducibility of topography and surface bioactivity from on-site treatment (Figure 2). In the future, for the immune or osteoinductive-suppressed patients who suffer from complications of drug use and systemic diseases such as diabetes mellitus and other genetic disorders, the promising biological effects from on-site surface functionalized Ti dental implant with nanotopography can be applied for enhancing success of osseointegration of Ti dental implant. However, in vivo and preclinical studies are insufficient to show promising effects for clinical application. Additionally, bacterial resistance effect on roughened Ti in the nanoscale from surface functionalization remains still under investigation. Further preclinical and clinical studies in terms of osseointegration and bacterial resistance are needed.

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Disclosure

Byung Gyu Kim and Seog-Jin Seo are co-first authors.

Competing Interests

The authors declare that there are no competing interests regarding the publication of this article.

Acknowledgments

This research was supported by Basic Science Research Program through the National Research Foundation of Korea (NRF) funded by the Ministry of Education (Grant no. 2009-0093829) and Research Fellowship Program (NRF-2013R1A1A2062694).

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Copyright © 2016 Byung Gyu Kim et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

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