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|[ Original Article ]|
|Korean Journal of Dental Materials - Vol. 49, No. 2, pp. 63-76|
|Abbreviation: Kor J Dent Mater|
|ISSN: 2384-4434 (Print) 2384-3268 (Online)|
|Print publication date 30 Jun 2022|
|Received 10 Jun 2022 Revised 28 Jun 2022 Accepted 30 Jun 2022|
|Surface characteristics of plasma electrolytic oxidized Ti-mesh for dental use|
Chang-Su Seo1 ; So-Ra Lee2 ; Han-Cheol Choe1, *
|1Advanced Functional Surface & Biomaterials Research Lab, Department of Dental Materials & Research Center of Surface Control for Oral Tissue Regeneration (BRL Center of NRF), College of Dentistry, Chosun University, Republic of Korea, Gwangju, Republic of Korea|
|2Department of Periodontology, College of Dentistry, Chosun University, Republic of Korea, Gwangju, Republic of Korea|
전해산화처리된 치과용 Ti-메쉬의 표면특성
서창수1 ; 이소라2 ; 최한철1, *
|1조선대학교 치과대학 구강조직재생 표면제어연구센터 및 치과재료학교실|
|Correspondence to : *Han-Cheol Choe 309 Pilmun-daero, Gwangju 61452, Republic of Korea Affiliation: Advanced Functional Surface & Biomaterials Research Lab, Department of Dental Materials & Research Center of Surface Control for Oral Tissue Regeneration (BRL Center of NRF), College of Dentistry, Chosun University, Republic of Korea, Gwangju, Republic of Korea Tel: +82-62-230-6896, Fax: +82-62-230-6896 E-mail: firstname.lastname@example.org|
Funding Information ▼
In this study, surface characteristics of plasma electrolytic oxidized Ti-mesh for dental use were studied using various experimental instruments. The titanium mesh was used as a substrate for PEO. Using a pulsed DC power supply, PEO treatment was carried out at 280 V for 3 min in the electrolytic solution containing Ca, Mg, and P ions. And the electrolyte used for PEO was prepared by mixing with Ca(CH3COO)2·H2O, C3H7CaO6P, and (CH3COO)2Mg·4H2O. The PEO-treated surface was observed by using X-ray diffraction, field-emission scanning electron microscope, energy dispersive X-ray spectroscopy, atomic force microscopy (AFM), and nanoindentation tester.
PEO-treated Ti-mesh in solution containing Ca, Mg, and P ions (CaMgP) sample showed the active spark discharge reaction compared to in solution containing Ca and P ions (CaP) sample. In CaP and CaMgP samples, the PEO surface of Ti-mesh showed mainly circular, irregular, and oval shapes of pores. In the case of CaMgP, the defects and precipitates such as MgO were formed on the surface. On the sample surface, the distribution of the desired element was detected homogeneously. The PEO-treated CaP and CaMgP specimens were mainly composed of anatase, Mg, and hydroxyapatite. From the AFM result, the average roughness was 0.247 μm for CaP and 0.226 μm for CaMgP, respectively. The hardness of CaMgP containing Mg ions was increased compared to CaP containing without Mg ions, also, the elastic modulus of CaMgP sample was higher than that of CaP sample.
본 연구에서는 전해산화처리된 치과용 Ti-메쉬의 표면특성에 관한 연구이며, 이를 위하여 티타늄메쉬를 PEO 처리용 기판으로 사용하였다. 펄스 DC 전원을 사용하여 Ca, Mg 및 P 이온을 포함하는 전해액에서 280 V에서 3분 동안 PEO 처리를 수행하였으며 PEO 처리에 사용된 전해질은 Ca(CH3COO)2·H2O, C3H7CaO6P, (CH3COO)2Mg·4H2O를 혼합하여 제조하였다. PEO 처리된 표면은 X-ray diffraction, field-emission scanning electron microscope, energy dispersive X-ray spectroscopy, atomic force microscopy (AFM), 및 nanoindentation tester를 이용하여 조사하였다.
Ca, Mg 및 P 이온(CaMgP)을 포함하는 전해액에서 PEO 처리된 Ti-mesh는 Ca 및 P 이온(CaP)을 포함하는 전해액에서 처리된 것에 비해 활성 스파크 방전 반응을 보였으며 CaP와 CaMgP 용액에서 처리된 Ti-mesh의 표면은 주로 원형, 불규칙, 타원형의 기공을 보였다. CaMgP의 용액에서 처리된 경우 표면에 MgO와 같은 결함 및 석출물이 형성되었다. PEO 처리된 표면에서 원하는 원소의 분포가 균일하게 검출되었다. PEO 처리된 CaP와 CaMgP 시편은 주로 anatase, Mg, hydroxyapatite로 구성되었다. AFM 결과에서 평균 거칠기는 CaP의 경우 각각 0.247 µm, CaMgP의 경우 0.226 µm였으며 Mg 이온을 포함하는 CaMgP의 경도는 Mg 이온이 포함되지 않은 CaP에 비해 증가하였으며, CaMgP 샘플의 탄성 계수도 CaP 샘플보다 높게 나타났다.
|Keywords: Plasma electrolytic oxidation, Micro-pore formation, Hydroxyapatite, Magnesium, Titanium mesh
키워드: 전해산화처리, 마이크로 기공 생성, 하드록시아파타이트, 마그네슘, 티타늄 메쉬
Ti and Ti alloys are currently the most commercially used materials. In particular, since it has good corrosion resistance and biocompatibility, many studies are being conducted to apply it to medical devices for dental and orthopedic implants (1, 2). However, since Ti is a bioinert metal, direct binding to living bones can lead to inflammation and allergy symptoms (3). The biological activity of Ti and its alloys mainly depends on the structure, shape and chemistry of the surface layer (4). Ti has a much higher modulus of elasticity than pure bone, but the lowest modulus of elasticity compared to other metals (5). Ti-mesh is used in the implant procedure in the dental area and it is used to extract teeth or to transplant bone to a patient with low bone density. At this time, the mesh requires two requirements. It must have excellent biocompatibility on the surface, and it must be removed well when a certain amount of time has elapsed after surgery. Because it has to be well attached to the bone, it requires an excellent biocompatibility on the surface.
Therefore, in order to improve the bioactivity of Ti surface, surface modification of Ti mesh has been researched to increase the bonding strength between bone and mesh surface and prevent various side effects such as inflammation and allergies (6, 7). A surface modifications for improving bioactivity of Ti-mesh are physical vapor deposition (PVD), chemical etching, titanium plasma spraying (TPS), titanium sintered pore coating, RF-sputtering, anodizing, resorbable blasting media (RBM), and sandblasting (5). Among these methods, the plasma electrolytic oxidation (PEO) method can produce thick, hard, and strong oxides by the electrochemical oxidation process by variously controlling the applied voltage, current, time, and temperature with a relatively simple experimental method and low cost (8). PEO film can be formed on light metals and alloys in aqueous electrolyte solutions under plasma discharge conditions that exceed the threshold of polarization potential. Due to this reaction, during the PEO process, Ca2+ and PO43- ions react through the micro-discharge potential generated at high temperature through Ca and P ions on the Ti surface to form a hydroxyapatite (HA) phase as a coating (9, 10). In addition, Mg ions play an important role in bone metabolism as they affect osteoblast activity. Previous studies have found that Mg ions are one of the substances that enhance bone formation in Ti alloys. It is predicted that there will be a difference in bioactivation when PEO is performed in a solution containing Ca and P ions and in a solution containing Ca, P and Mg ions, and this difference can be predicted through changes in physical and biological properties. However, a few studies on this have been reported, so we intend to investigate it in this study.
Therefore, in this study, surface characteristics of plasma electrolytic oxidized Ti-mesh for dental use were studied using various experimental instruments.
Ti-mesh were used as substrates for PEO treatment. Prior to nanotube formation and PEO treatment, each Ti-mesh specimen was initially polished from #100 to #2000 using various grades of standard ANSI SiC. And then, the specimen was wet-polished with 1.0 μm alumina powder (Al2O3), ultrasonically cleaned with deionized water, and finally the specimen was dried under flowing nitrogen. The prepared specimen was used for micro-pore formation. The polished mesh was thoroughly with distilled water and ultrasonicated for 5 min in ethyl alcohol. Under a pulsed DC field (DC power supply, Keysight co., Ltd., USA) the best voltage condition in the PEO process is 280 V for 3 min. The composition of the electrolyte used in the PEO process was shown in Table 1. It shows the electrolyte concentrations of Ca(CH3COO)2·H2O, C3H7CaO6P, (CH3COO)2Mg·4H2O for Ca, P, Mg doping on the surface. In this study, sample names of CaP and CaPMg was used for Ca, P, and Mg doping, respectively. The samples were connected to the positive terminal of the power source and a platinum rod were connected to the negative terminal of the power source. The temperature of the electrolyte was kept below 25 ℃ by a cooling system. The PEO films formed on samples were flushed with water after the treatment and dried in warm air.
|Experimental Condition||Composition of Electrolyte|
The PEO morphologies of the sample surface were observed using field emission scanning electron microscopy (FESEM; Hitachi4800, Japan) and energy-dispersive X-ray spectroscopy (EDS; Hitachi4800, Japan). FESEM observations were performed at an operating voltage of 15 kV and a scan speed of 40 s. EDS observations were carried out at an operating voltage of 15 kV and a live time of 30 s. The crystalline structure of the specimens was identified with the aid of a thin film X-ray diffraction with radiation from a Cu target (Kα, λ= 1.5406 Å). The crystal structure of the specimen was determined by an X-ray diffraction analyzer (XRD; X-ray diffraction, X'pert PRO, Philips, Netherlands) was used, and the scan range was analyzed in the 2θ section of 20 to 80 degrees. XRD patterns of peaks were interpreted with the aid of published JCPDS information for powder standards. The hardness and elastic modulus of each alloy were measured using a nanoindentation tester (TTX-NHT3, Anton Paar, Austria). The maximum load of the sample was set to 20 mN and the stop time was set to 5 seconds. Each sample was measured four times to obtain an average value and a standard deviation. The surface shape and roughness were measured and analyzed using the XE Data Acquisition program using an atomic force microscope (AFM, Park XE-100, Park Systems, Korea). The scan size of the surface roughness measurements was ~15.00 μm and the scan rate was 0.40 Hz. AFM measurements were performed in non-contact mode.
Figure 1 shows the PEO coating process from 0 to 3.5 seconds. In this process, it was seen that the PEO film was rapidly formed at the beginning of the coating under the PEO condition of 280 V for 180 seconds due to a change in plasma discharge and electrolyte polarity, and then stabilized thereafter. In the Figure 1, it can be seen that the case of doping with Ca and P (a) and the case of doping with Ca, P, and Mg (b) show similar spark discharge patterns, but when Mg is added, the reaction is stronger and more active compared to CaP sample. This can be judged to be due to a change in the composition of the electrolyte, and it is thought that Mg is formed on the surface by contributing to the passivation film formation process on the surface by adding Mg.
In the PEO process, the pore formation process is affected by various conditions, and the mechanism is explained as follows (11) ; the PEO steps were to form and grow a passivation film on the substrate as a result of applying an extremely high voltage to the electrolyte. As the thickness of the oxide layer increased, the voltage between the substrate and the electrolyte increased. The weak part of the oxide layer will suffer dielectric breakdown due to the high voltage. The oxide layer melted by the high temperature generated in the micro-discharge region tends to be ejected from the substrate coating interface to the coating surface, leading to rapid solidification and recrystallization by the cooling electrolyte. After all, it is possible to obtain coatings composed of complex compounds in various electrolytes. In the case of PEO-treated surface in solution containing Mg ions, MgO can be formed in the oxide film by sparking of anodic oxidation. At high temperatures, MgO is present in a fused state, but during the spark of anodic oxidation and spacing of micro-arcs, due to the cooling effect of the electrolyte (12). From the research on PEO-treated Mg alloy (16), the alkaline treatment of the PEO coatings of pure Mg could lead to the formation of Mg(OH)2 on the coating surface. The formation of Mg(OH)2 did not generate any detrimental effect on the cytocompatibility in cell culture medium. Mg is generally known as a bioactive element, so it is expected to play a role in increasing biocompatibility even if it forms an oxide.
Figure 2 shows the FESEM images of PEO-treated Ti-mesh surface in electrolyte containing Ca and P ions at 280 V for 3 min. Figure 2 (a) shows the entire surface at low magnification, (b) enlarges it and observes the distribution of pores, and (c) and (d) shows the observation of round, oval, and irregular shapes of pores. Although the shape of the pores is mainly circular, the reason for such an irregular shape is considered to be various factors related to the PEO process. It has been reported that the size and shape of the pores formed in the oxide layer depend on the composition and concentration of the electrolyte and depend on the elements of the alloy (14, 15). In the PEO process, the pore size is determined by the formation and discharge of the oxide film in several stages. For example, there are cases in which secondary pores are formed again in the pores formed in first pores, so that the pores are enlarged and small pores are present. By repeating the process of forming other pores within the first pore as described above, micropores having different sizes and shapes can be obtained. The surface of the PEO (CaP) specimen showed many pores, and no sediment was observed on the surface in the enlarged figures, and pores could be formed in a short time. As shown in Figure 2, the size of the pores is uniform and the size of the nano-particles grows evenly, indicating that it is consistent with the previous study (14).
Figure 3 shows the FESEM images of PEO-treated Ti-mesh in electrolyte containing Ca, P, and Mg ions at 280 V for 3 min. Figure 3 (a) shows the entire surface at low magnification, (b) enlarges it and observes the distribution of pores, and (c) and (d) shows the observation of round, oval, and irregular shapes of pores. In Figure 3 (a), compared to Figure 2 (a), the surface is much roughened. In order to confirm this, it can be seen from the Figure 2 (b) that the surface was formed in the same manner as a defect on the surface due to the active PEO reaction. In Figure 3 (c) and (d), it can be seen that a lot of things such as precipitates are covered on the surface. It is considered that Mg was added and not only doped inside during the PEO process, but also formed precipitates such as MgO on the surface. What is unusual is that the size of the pores formed on the surface is greatly increased. This is because it is a case of treatment in an electrolyte solution to which Mg active element is added. It is expected that it will be good for osteoblast activity, which is important for bone metabolism, due to the pores that appear to be many Mg precipitates on the surface (16). Therefore, the microstructure of the generated PEO layer depends on the type of micro-discharge in the PEO process, and the composition of the electrolyte such as Mg affects the morphology of PEO and the change in the size of the pores (11).
Figure 4 and 5 show the EDS peaks and mapping images of PEO-treated Ti-mesh in electrolytes containing Ca, P, and Mg ions. In Figure 4, (a) shows a CaP sample and (b) shows a CaMgP sample, respectively. Overall, the distribution of the desired element is detected homogeneously, and in particular, in the case of CaMgP specimen, Mg is detected and the coating seems to be good. In addition, it can be seen that the pore size is significantly increased compared to that of the CaP specimen. In Figure 5, (a) shows a CaP sample and (b) shows a CaMgP sample. As shown in Figure 5, in the case of CaP specimen, Ca and P elements were uniformly distributed in the pores and surface, whereas Mg was mainly detected at the surface, which is in good agreement with the precipitates shown in Figure 3.
Figure 6 shows the X-ray diffraction peaks of PEO-treated Ti-mesh of (a) bulk, (b) CaP, and (c) CaMgP, respectively. All patterns of XRD were confirmed by comparing with JCPDS (Joint Committed on Powder Diffraction standards, PCPDFWIN), HA(ICSD #083352, #026261), Ti(#7440-32), TiO2-rutile (ICSD #085494, #085495, #082656), TiO2-anatase (ICSD #202243, #202242, #200392), Mg(#35-0821). The PEO-treated specimen was mainly composed of anatase and HA, and it was determined that the oxide film formed during the PEO process had an anatase structure to improve biocompatibility. In CaP and CaMgP samples, anatase peaks were observed at 2θ= 25.00 and 25.55°, and HA peaks were observed at 2θ= 29.28 and 29.84°, respectively. And Mg was observed at 2θ = 36.62, 67.31 and 68.63°, respectively, and it can be seen that it is in good agreement with the Figure 3 in which Mg is covered on the surface. In particular, lattice matching of anatase structure and HA structure in the PEO process is known to induce early bone adhesion and growth, so it is expected that the initial biocompatibility will be improved. In addition, as mentioned at the beginning, there is an Mg peak, which is expected to improve biocompatibility (11).
Figure 7 shows the surface images AFM(atomic force microscopy) of PEO-treated Ti-mesh (a) CaP and (b) CaMgP. The respective average roughness values were 0.247 μm for CaP and 0.226 μm for CaMgP. The surface roughness of CaMgP measured by AFM showed slightly low, but in reality, the roughness of the defected surface is high as shown in Figure 3. This is thought to be small because the size of the pores is large and the small pores are reduced, if the pores are large, measuring the roughness in nano-units scans the surface rather than the pores.
It can be seen that the roughness increases when PEO(CaP and CaMgP) is treated. This is considered to be due to the pores formed on the surface. In the case of coating with Mg, the surface roughness is increased. Surface roughness greatly affects biocompatibility, and an average roughness value within 5 micrometers is recommended for biocompatibility.
Figure 8 shows the results of nanoindentation test to determine the elastic modulus and indentation hardness. The load-displacement graphs can be known as stiffness, contact area, modulus, and hardness etc. The stiffness and elastic modulus are determined according to the slope, and the larger the value of the slope, the stronger the stiffness and the weaker the elastic modulus (7). Figure 8 (a) shows that the stiffness weakens and the modulus of elasticity increases from the bulk to the PEO-treated CaP and CaMgP. This shows that the HA deposition on the surface is good and that HA is more ductile than the conventional Ti-mesh. Therefore, it is seen that CaMgP containing Mg ions is stronger than CaP containing without Mg ions. In general, the modulus of elasticity increases as strength and hardness increase. However, Mg increases the size of pores due to strong electrical stimulation caused by anodization, resulting in larger pores than CaP. When measuring the hardness of the surface, it is also affected by the presence or absence of pores, but when Mg is added, it is thought that the surface is doped with Mg element, resulting in an increase in hardness or an increase in elastic modulus due to solid solution hardening. The inorganic material layer manufactured through PEO technology is expected to provide excellent hardness and adhesion due to properties similar to ceramics having a relatively thick and dense structure. In the case of Mg alloy, it is reported that MgO and Mg3(PO4)2, contribute to hardness (17). Hardness and adhesion values can vary with substrate condition, electrolyte composition, current density, and processing time, which determine the major phase components (18). Therefore, when PEO treatment is performed in an electrolytic solution containing Mg, the formation of Mg oxide is increased, hardness is increased, and as a result, it is considered that the elastic modulus is increased.
CaMgP sample showed the active spark discharge reaction compared to CaP sample. In CaP and CaMgP samples, the PEO surface of Ti-mesh was mainly circular, irregular, and oval shapes of pores. In the case of CaMgP, the defect and precipitates such as MgO was formed on the surface. On the surface of sample, the distribution of the desired element was detected homogeneously, and in particular, in the case of CaMgP specimen, Mg was detected and the coating seems to be good. In the case of CaP specimen, Ca and P elements were uniformly distributed in the pores and surface, whereas Mg was mainly detected at the surface.
The PEO-treated specimen was mainly composed of anatase and HA, in CaP and CaMgP, anatase peaks were observed at 2θ= 25.00 and 25.55°, and HA peaks were observed at 2θ= 29.28 and 29.84°, respectively. And Mg was observed at 2θ = 36.62, 67.31 and 68.63°, respectively. From the AFM result, the average surface roughness was 0.247 μm for CaP and 0.226 μm for CaMgP. CaMgP containing Mg ions was harder than CaP containing without Mg ions, also, elastic modulus of CaMgP sample was higher than that of CaP sample.
This research was supported by Chosun University 2022.
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