KR101092227B1 - Metal surface treatment method and the metal treated thereby - Google Patents

Abstract

The present invention relates to a surface treatment method for coating a bioactive material on the surface of a metal. The present invention can induce differentiation into the corresponding tissue cells such as osteoblasts, osteoblasts, stem cells, etc., as well as coating a bioactive material for enhancing the adhesion of bone cells, cleanly washed titanium, And annealing the metal including titanium, the ceramic containing titanium oxide and titanium oxide, with an alkali solution including sodium hydroxide, and the like.

Metal surface treatment, bioactive material, medical equipment

Description

Metal surface treatment method and the metal treated thereby

The present invention relates to a surface treatment method for coating a bioactive material on the surface of the metal and a metal coated with the bioactive material.

Bioactive coatings can be broadly divided into bioactive inorganic coating and bioactive organic coating. Bioactive inorganic coating is a method of imparting bioactivity to the surface by fixing it to the surface of the metal by plasma spray method, sol gel method, vacuum deposition method, etc. The bioactive organic coating is applied to the surface of the metal with hydrogen peroxide and silane, etc. A method of chemically sharing bioactive organics.

Bioactive inorganic coatings are a method of immobilizing bioactive minerals on surfaces by physical methods. Bioactive materials immobilized by physical methods induce cells of living tissue to mistake the object as a 'part of the living body' rather than as a foreign body, and the cells of living tissue are more friendly than a reaction to an object whose surface is made of an inert material. Approach to induce the function of the object as a living implant faster. However, bioactive minerals have limitations that do not induce differentiation of stem cells and other tissue cells. Accordingly, research on bioactive organic coating has been recently promoted.

The basic skeleton of the bioactive organic coating is as follows. First, the chemical activity is imparted to the surface of the metal with hydrogen peroxide and silane (surface fixation of a functional group such as hydroxyl group or amine group), and then the bioactive organic coating is finished by chemically bonding to a specific functional group of the bioactive organic material. Such reactions have limitations that apply only to simple peptides with several amino groups because they can induce uncontrolled side reactions on very complex and large molecules such as proteins. Fixation of simple peptides induces adhesion with adhesion proteins (fibronectin, integrin) on the cell surface by assigning the sequence of RGD, but does not induce 'differentiation of stem cells, etc. into the corresponding tissue cells' as mentioned above. It has the same limitations as bioactive inorganic coatings.

The initial goal of bioactive organic coatings (promoting differentiation of stem cells, etc. into corresponding tissue cells) can be achieved by immobilizing growth factors or similar proteins on the surface of the implant, and chemical fixation of such bioactive proteins is controlled. This is avoided because of the possibility of inducing side reactions that do not occur. Therefore, in the publications of various papers and the like, only the surface on which the bioactive protein is dried is presented by simply dropping the solution containing the bioactive protein on the surface of the metal and then drying the solution. Proteins immobilized in this way have a very poor adhesion to metal and disappear into the tissue very quickly when implanted into the tissue. Not only does this mean that the immobilization of the bioactive protein to this plant is not permanent, it melts, even if it is assumed that the bioactive protein that has adhered to the surface of the implant and migrated into the biological tissue melts into the biological tissue. The speed of exit is very fast at the beginning, so that the bioactivity cannot be imparted for a long time.

The present invention is to coat the bioactive material for inducing differentiation into the corresponding tissue cells, such as stem cells, 1) the surface treatment process of the biograft (metal) as its pretreatment and 2) the unique treatment obtained by the surface treatment process 3) develop a method of enhanced bonding between the surface and the physically and chemically strengthened metal surface by the bioactive material and the unique surface.

The present invention not only induces differentiation into osteoblasts, osteoblasts, stem cells, etc. into the corresponding tissue cells, but also in the coating of a bioactive material for enhancing the adhesion of osteoblasts, cleanly washed titanium, The present invention provides a process for surface treatment suitable for coating a bioactive organic material by treating the metal including titanium and the ceramic containing titanium oxide to titanium oxide with an alkali solution including sodium hydroxide and the like followed by annealing.
According to an aspect of the present invention, there is provided a method for treating a surface of a metal, the method comprising: treating the titanium or the metal including the titanium with an alkaline solution containing 1 to 10 mol / L of high concentration sodium hydroxide (NaOH); And annealing the metal material surface-treated with the alkaline solution, wherein the surface treatment step includes etching the metal material through the alkaline solution at a high temperature of 18 ° C to 90 ° C.
At this time, the degree of the etching is controlled by the time the metal is immersed in the alkaline solution, the time is implemented over a few hours to several days, the annealing step is 900 under an atmosphere containing air or oxygen It is characterized in that it is carried out at a temperature of less than.
The method may further include coating a bioactive organic material on the metal material on which the surface treatment and annealing is completed, wherein the bioactive organic material may include several to several tens of amino groups including an RGD (Arg-Gly-Asp) sequence. Peptide containing; Growth factors such as FGF (Fibroblast Growth Factor Family); It is characterized in that it comprises at least one or more of four groups consisting of bone-induced proteins and adhesive proteins such as BMP (Bone Morphogenetic Protein Family).

Modification effect of the metal surface obtained by the surface treatment process is largely divided into physical effects and chemical effects. As a physical effect, surfaces such as coarse projections finely etched below micrometers and cracked surfaces, such as traps etched beyond micrometers, have bioactive organics that act as hooks or maximizes as if fish caught in fish hooks cannot escape. By providing a surface area, the adhered organic matter is extremely suppressed from falling off. As a chemical effect, the hydrated surface chemical structure produced by alkali treatment induces hydrogen bonds to all bioactive organics, thereby enhancing the metal-organic bonds that are strengthened, rather than simply immobilized by simple Wan der vaals forces. Can be achieved.

On the other hand, as a physico-chemical effect, the surface modified with alkali having an elevated surface energy has very high hydrophilicity, and when the distilled water droplets are dropped on the surface, it shows excellent wettability that does not drop on the surface of the metal and spreads quickly. Similarly, when the implant is implanted in living tissue, body fluids, as well as biomolecules such as various growth factors and adhesive proteins (fibrin, integrin, fibronectin, etc.) in the blood, are modified on the surface of the implant. By sticking well, an improved joint can be obtained.

The present invention conceptually provides a method of coating a bioactive material on 1) the surface treatment of a biograft (metal) as its pretreatment and 2) the unique surface obtained by the surface treatment process and 3) the bioactive material and the unique surface. By the development of a method of strengthening the bonding between the physically and chemically strengthened metal surface by the three, etc., the process actually introduced to obtain this is very simple.

Cleanly washed titanium, metals containing titanium, ceramics containing titanium oxide to titanium oxide, and alkaline solutions of high concentrations (especially 1 to 10 mol NaOH / 1 L of clean water) containing sodium hydroxide and the like at room temperature to 90 ° C. Etch over a high temperature solution for several hours to several days, and finish the surface treatment process of the metal by washing the etched metal with clean water, or 900 ℃ in the atmosphere containing the atmosphere to oxygen to stabilize the surface The surface treatment process of metal is complete | finished by annealing over several ten minutes-several days at the following temperature.

After the surface treatment of the metal is finished, growth factors such as peptides including FRGs (Fibroblast Growth Factor Family) containing several to several tens of amino groups including RGD (Arg-Gly-Asp) sequences, and BMPs (Bone) Natural body fluids are exposed to the surface of metals by exposing similar body fluids containing bioactive organic molecules such as bone-induced proteins such as Morphogenetic Protein Family) or biomolecules such as adhesive proteins (fibrin, integrin, fibronectin, etc.) to the surface of the metal. The bioactive organic molecules are fixed to the surface of the metal by drying, heat drying, freeze drying or reduced pressure drying.

Hereinafter, an embodiment of the surface treatment method and the organic coating method will be described in more detail.

First, the metal which is cleanly washed titanium to titanium is surface-treated with an alkaline solution containing sodium hydroxide or the like.

At this time, the alkaline solution may be a solution containing a high concentration of sodium hydroxide, such as clean water of 1 to 10 mol / L NaOH.

At this time, it is preferable to form an etching environment at a high temperature ranging from room temperature (18 ° C) to 90 ° C in the alkaline solution treatment step.

At this time, it is preferable that the alkaline solution treatment process proceeds over 1 hour to 10 days. For example, it may be 1 hour to 24 hours, 3 to 5 days and the like.

Next, the alkali-treated metal is annealed.

When annealing a metal object, it is preferable that it is an atmosphere of an annealing process containing air and oxygen. Moreover, it is preferable to process the temperature at this time at the temperature of 900 degrees C or less. At this time, the annealing process preferably takes several tens to several days.

Next, a process of coating the bioactive organic material on the metal implant whose surface treatment is finished only by the alkali process or the metal implant whose surface treatment is finished by the alkali process and annealing process is required.

At this time, the bioactive organic material is derived from bone derivatives such as peptides containing several to tens of amino groups including the RGD sequence, growth factors such as FGF (Fibroblast Growth Factor Family), and BMP (Bone Morphogenetic Protein Family). Biomolecules such as proteins to adhesive proteins (fibrin, integrin, fibronectin, etc.). The bioactive organics are delivered to the surface of the metal modified surface in a buffer solution similar to the body fluid to keep them stable.

Next, a drying process is performed by natural drying, air circulation drying, heat drying, freeze drying to reduced pressure drying, and the like of the bioactive organics contained in the buffer solution transferred through the bioactive organic coating process.

This improves the adhesion from the mechanical point of view of the bioactive organic molecules due to the peculiar rough surface of the micrometer or less and the micrometer or more obtained by the alkali treatment, and the chemical activity of the bioactive organic molecules by the hydrated metal surface obtained by the alkali treatment. Adhesion from the viewpoint is improved, and the physical / chemical wettability of the bioactive organic molecules due to the very hydrophilic surface obtained by alkali treatment is improved.

1 is a scanning electron micrograph of a metal surface chemically surface-treated for bioactive coating. According to this, the surface-treated metal surface has both a rough surface finely etched to the micrometer and a cracked surface such as a trap etched to the micrometer or more. Provides a hooked or maximized surface area, such as no escape.

2 is a contact angle photograph when water droplets are dropped onto the metal specimen before the metal surface treatment according to the present invention, Figure 3 is a contact angle photograph when water droplets are dropped onto the metal specimen treated metal surface according to the present invention. .

According to this, the contact angle of ultrapure water droplets to the bare titanium surface before alkali treatment is about 62 °, while it is very hydrophilic at about 20 ° when treated at 60 ° C for 6 hours with 5 mol NaOH / 1L. A surface with high surface energy was obtained. That is, according to the present invention, the physical / chemical wettability of the bioactive organic molecules due to the hydrophilic surface is improved, so that when the bioactive organic molecules / surface-treated titanium interface with the bioactive organic molecules / surface treated titanium It is confirmed that it is formed.

The following description can clearly understand that it can be easily applied to the implant as an application of the present invention.

Titanium Plasma Spray (TPS) using titanium powder is the first surface treatment to increase the roughness and surface area in order to have a higher bone joint for machined implants. This method injects titanium hydride powder into a very high temperature plasma (about 1500 degrees or more) formed by arc discharge. Titanium hydride decomposes in the hot plasma, and titanium metal particles of 50 to 100 µm in size adhere to the body surface of the implant. The immobilized titanium particles increase the mechanical interlocking performance by increasing the roughness and surface area of the implant surface. The surface layer thus formed has a thickness of about 30 to 50 μm, and has a roughness of about 15 μm. It is continuously round, connected to each other, and made of porous material. Through this process, the surface area of the implant is increased by 6 to 10 times. However, implants to which the TPS coating method is applied cause desorption of the coated titanium particles in tissues after embedding, causing problems such as inflammatory reactions. For this reason, it is not currently used.

With the introduction of TPS in the 1980s, various implants coated with hydroxide apatite were also recommended for clinical use. Hydroxyapatite coating by plasma spraying method, compared with pure titanium implants, was coated with hydroxide apatite that is chemically and crystallographically identical to the mineral component of bone, thereby improving bone bonding ability between bone and implant as well as increasing bone recovery.

Various clinical studies have shown that the coating of hydroxide apatite shows excellent clinical results early in the meal. Hydroxyapatite-coated implants exhibit a bioactive surface structure that results in faster bone recovery compared to metal implants. However, similar to the TPS system, the hydroxide apatite-coated layer coated by plasma spraying method is currently being avoided due to the mechanical instability of the coating layer in body fluids such as desorption of the coating layer. If a problem such as desorption of the coating layer occurs, an inflammatory reaction occurs and bone absorption occurs around the implant, thereby causing a problem of bone loss.

In order to increase the roughness and surface area of the implant, a blasting method (sand spray) may be used. If the plasma spraying method is a method of coating small titanium powder, the blasting method is to cut the surface of the implant to control the surface roughness and surface area. It is an important advantage that the process of slicing the surface of the implant to make the roughness can avoid the problem of 'taliberization' of the coating that occurs in the coating method. Although the blasting method has an advantage of controlling the surface roughness by using alumina powder, titania powder, etc. of a specific size according to the purpose, there is a disadvantage that the blasting particles remain on the surface. In order to solve the problem of residual blasting particles, acid corrosion is applied in a subsequent process. The combined process of blasting and acid corrosion is commonly referred to as sand blasted large-grid acid-etched (SLA). 4 shows a photograph of a Ledermann implant surface treated by blasting and acid corrosion, and FIG. 5 compares the surface state of the acid treatment after blasting.

Another way to solve the problem of blasting particle retention is to use absorbed particles. One system using absorbed particles is Restore's Resorbable Blasted Media (RBM) surface treatment. When calcium-phosphate powder is used, even if the powder remains on the implant surface, it is absorbed by the body when buried in the body and does not cause a big problem.

Ster-Oss, 3i, and Biohorizon DI include systems that apply erosion to the roughness of surfaces. All three systems exhibit roughness of 1 to 2 μm.

An excimer laser is also used to roughen the surface of the implant. The advantage of using a laser is that it can be aimed precisely in a predetermined direction, and it is also possible to form a microstructure in a predetermined arrangement. 6 shows the surface of titanium treated with a laser. The regular surface structure shown in the picture was chosen in an attempt to create a physiologically retaining structure similar to natural bone shochu.

Forming pore on the surface to grow bone inside the pore to obtain a three-dimensional bone adhesion has also been applied in clinical recently. The Endopore implant system is very unique. Spherical titanium particles of about 44 ~ 150 ㎛ are sintered in vacuum at 1250 ℃ and have a pore depth of 150 ~ 300 ㎛, and bone cells grow inside the pores and have a very wide contact area. The system can also be used for areas with poor bone quality or low amounts of remaining bone. The Branemark threaded implant with a length of 12 mm and a diameter of 4 mm has a surface area of 248 mm ^2, but the surface area of Endopore with a length of 12 mm and a diameter of 4.1 mm is 781 mm ^{2, which} is more than three times larger and can withstand loads.

Anodization is another way of forming pores on the surface and growing bones into the pores to achieve three-dimensional bone adhesion. The Ti-Unite implant system uses anodization, which electrochemically oxidizes the surface of titanium implants. When the applied electric field is high, micro-arc is generated on the surface, which makes the pore structure of the oxide film.

Recent trends in dental implant development have centered on enhancing biocompatibility of surfaces facing the alveolar bone. To date, research on tooth transplantation has continued, but it has not been popularized due to its low success rate. However, after Branemark of Sweden announced a titanium-based bone adhesion implant in Toronto, Canada in 1982, the implant procedure became popular worldwide with clinical success rates exceeding 90%. From this point on, research and development of a full-scale dental implant began.

Dental implants are biomaterials that replace the teeth of the human body. Therefore, the conditions that the implant must have are divided into the inherent properties (physical and mechanical properties) of the material itself, the shape of the implant (mechanical properties), the reaction with body fluids (chemical properties), and the reaction with biological tissues (biological properties). can see.

As an artificial tooth, the implant must have the same properties as the base material (density, strength, tensile stress, compressive stress, elasticity, fatigue properties), or the like. For example, if the strength of the base material is very large, the alveolar bone around the implant is lost, and if the strength of the base material is insufficient, the destruction of the implant occurs. Most implants are threaded into the alveolar bone to be implanted. At this time, the thread design is careful not to cause detachment of the implant despite the continuous chewing movement. On the other hand, in order to enhance the mechanical adhesion with the alveolar bone, the surface may be roughened.

Implants embedded in the alveolar bone are in contact with body fluids, macrophages, osteoclasts, osteoblasts, and the like. First and foremost, the implant must not have unwanted corrosion on body fluids (where unwanted corrosion means corrosion, except for the dissolution of it by coating soluble CaP to induce osteoblasts). Since body fluid is an aqueous solution in which a wide variety of ions are dissolved, chemical resistance of the implant surface must be ensured in order not to cause such corrosion problems. On the other hand, the implant should not cause rejection from the tissue of the implanted site including the alveolar bone. This means that the implant should not have cytotoxicity and should have biocompatibility, and a lot of recent research has been focused on improving bio-activity as well as bio-compatibility of osteoblasts.

The conditions that the dental implant must have are summarized in Table 2 below by dividing the physical, mechanical, chemical and biological characteristics.

Table 2. Implant Development Elements

Physical properties Material Properties Material density, strength, coefficient of thermal expansion, etc.
-Surface roughness, pore distribution, specific surface area, etc.
-Coating layer thickness, composition, crystallinity, adhesion to the base material, etc. Mechanical properties Mechanical properties of the material -Tensile stress, compressive stress, elasticity, etc Characteristics of screw design -Thread depth, pitch, taper angle, unique design, etc. Chemical properties Corrosive Properties -Corrosion Characteristics of Metal Implants For analogous fluids
Reaction characteristics -Disappearance of the film or formation of a new film
-Change in surface composition, change in crystallinity, etc. Biological properties In vitro experiment -Proliferative characteristics of human derived osteoblast
-ALP (Alkaline Phosphatase) activity characteristics, etc Body experiment -New bone formation through histological analysis
-Activity characteristics of Osteoblast, osteoclast
RTQ (Removal Torque) characteristics
-RFA (Resonance Frequency Analysis) characteristics

Dental implants began with a medical engineering position to replace lost teeth. Thus, in the early stages of development, research focused on the appearance and mechanical properties of teeth. There have been many studies on the density, strength, tensile stress, compressive stress, elasticity, etc. of materials. On the other hand, even if it satisfies the mechanical properties it is a problem that must be solved not to cause a corrosion / rejection reaction in complex body fluids. The characteristics of various metals and metal alloys have been evaluated. As a result of these studies, titanium and titanium alloys have been recognized as the most potent materials.

As research on the selection of materials for dental implants has progressed sufficiently, the focus of the research has shifted its focus to improving the surface of implants. Implants that satisfy the mechanical properties of the teeth and do not cause rejection can be used as dental implants by themselves, but this is because the purpose of contributing to the improvement of the quality of life of patients by achieving excellent bone bonding as soon as possible. . This effort centers on improving the surface of the implant.

Surface modification of dental implants can be broadly divided into physical properties and chemical properties. The goal of the modification of physical properties is to enhance the bond between the implanted implant and the alveolar bone by controlling the surface roughness. Surface roughness control at the level of tens to hundreds of micrometers can enhance the mechanical adhesion performance so that it cannot be detached even if the bonding strength with the alveolar bone is insufficient, and roughness control at tens of micrometers or less makes the surface friendly with osteoblasts. Leave. In order to control the surface roughness, alumina powder, titania powder, calcium-phosphate powder, etc. of various particle sizes are sprayed to control the roughness of the implant surface, and the titanium powder is fired into the shape of the implant to make large pores. They may also be used to corrode the surface to produce a rough surface, or to combine it with the powder spraying methods mentioned earlier. However, the method of powder injection is one of the processes to be avoided as much as possible due to the problem of dust generated during the process.

The modification of the chemical properties is aimed at achieving rapid bone bonding by increasing affinity with osteoblasts and obtaining strong chemical bonds with bone minerals. Most implant surface treatments focus on the relationship between surface chemistry and osteoblast proliferation / characteristic expression. There are four main methods for modifying these surface chemistries. First, heat treatment of titanium to make titanium oxide strongly adhered to the base material into a specific crystalline phase, second, calcium-phosphate-based bioactive ceramics / glasses similar to the minerals of bone are coated by vacuum deposition method, and third hydroxyl on the surface And a fourth method of fixing a specific peptide.

When titanium is heat-treated, the oxide film formed on the surface can be made into amorphous, anatase, or rutile phases with a specific thickness according to the heat treatment temperature and time. Therefore, the crystal phase and thickness of the surface oxide film can be adjusted according to the purpose to improve reactivity with osteoblasts. Can be controlled. Since titanium oxide is bioinert, it is excluded from recent studies of bioactivity induction.

In case of coating calcium-phosphate-based bioactive ceramics / glass, the coated film may be dissolved / absorbed slowly in the body fluid depending on the composition and deposition method to create an environment favorable for the formation of hydroxide apatite. You can also increase the reactivity with osteoblasts by making the coating film of.

Hydroxyl groups introduced by various methods such as surface treatment in strong alkali or surface treatment using silanol and the like have been reported to not only increase the hydrophilicity of the surface but also help to form hydroxide apatite in body fluids. On the other hand, it has been reported that even when a specific peptide is immobilized through several steps of chemical surface treatment, it can induce strong binding to numerous proteins on the cell surface.

In addition, techniques for electrochemically treating surfaces have received much attention in recent years. This is a technique called micro-arc oxidation, in which a cut implant is placed in an electrolyte and an electric field is applied to react with the electrolyte at the surface to form an oxide layer. The generation of micro-arc due to a strong electric field is several hundred nm in the oxide layer. By creating pores in μm, rough surfaces can be created. In addition, the heat generated by the micro-arc is a process that can lead to a crystalline phase similar to the heat treatment of the oxide film at room temperature.

Table 3 summarizes the advantages and disadvantages of the various surface treatment techniques proposed for surface treatment of dental implants.

Table 3. Surface Treatment Technologies for Dental Implants

TECHNICAL NAME Advantages Disadvantages Rough machining Physical treatment
AS Threaded
Surface polished Lack of surface roughness (1 ~ 3㎛)
High failure rate
No bioactive material coating Sand blasting Physical treatment
Affordable Surface Roughness Control
Ease of Mass Production Poisoning by residue
No bioactive material coating Acid etching Physical treatment
Roughness around 1㎛
Ease of Mass Production Lack of surface roughness
No bioactive material coating Sintering Physical treatment
Very large specific surface area No bioactive material coating Plasma spray Chemical coating
Excellent bone formation effect even for poor bone quality
Short healing time
Roughness around 15㎛ Implant Base and Low Cohesion Pulsed laser deposition Chemical coating
High purity crystalline HA coating Economic and mass production difficulties
Still need a lot of research Bio-mimetic nano-composite Chemical coating
Same mechanism of regeneration as real bones Difficult to reproduce in mass production
Still need a lot of research Ion-beam assisted deposition Chemical coating
Enhance bond between coating layer and substrate by ion-beam during HA deposition
Surface shape of the base material is reflected as it is
Can be combined with physical processing
Nano-scale control possible Still need a lot of research Micro-arc oxidation Electrochemical Surface Oxidation Technology
Roughness Formation by Micro-arc
Heat treatment effect by micro-arc
Room temperature process High power consumption

As mentioned above, many medical and material engineers are currently striving to achieve fast recovery and strong bone bonding performance after implant surgery by enhancing the affinity for osteoblasts by changing the surface chemistry of the implant in various ways. Very good results have been reported by in vitro or in vivo experiments. Although not yet applied clinically, the clinical application of various chemical surface treatment techniques is estimated to be very imminent.

Characterization techniques for surface-modified dental implants are far behind. Many medical and material engineers suggest and apply various methods of evaluation of surface properties, but the evaluation techniques suggested by FDA's guidelines, ASTM, ISO, KS, JIS, etc. reflect recent research. There is no. If you look at the contents of these specifications, you can find the physical properties of implant materials (ASTM F138, F799, F1088, F1537), corrosion analysis of materials (ASTM STP684, STP859, F746, F1089, F1801, F2129) Related analytical methods (ASTM F748, F1027), adhesion measurement method of calcium-phosphate coating layer (ASTM F1147), physical property measurement method of calcium-phosphate coating layer (ASTM F1609), general property analysis method of biological glass / ceramic (ASTM F1538), XRD analysis of plasma sprayed hydroxide apatite (ASTM F2024). Most of the proposed analysis / measurement techniques are limited to measuring the properties of implant materials and adhesion analysis of coating layers, and do not include various surface property evaluation techniques proposed in recent research trends. This may be due to the lack of demand for clinical application of various types of surface treatment technology.

The position of implant surface treatment technology and dental implant evaluation technology that is applied in the clinic about the change of the implant development paradigm is schematically shown in Table 4 below. In many technological developments, research, development, and evaluation are common in that new paradigms are applied in that order. The same applies to the development of dental implants. In-depth research on surface modification is already underway in research and development, but there is still insufficient approach in clinical / evaluation technology.

Table 4. Location of Clinical Applications and Implant Assessment Technologies for Changes in Implant Development Paradigms

Early implant development Recent Implant Development Of research / development
Paradigm shift As an artificial tooth
Meet minimum requirements For improving bone bonding characteristics
Demand Satisfaction Satisfies mechanical properties as an artificial tooth
Biocompatibility Introduction of the concept of surface modification
Introduction of bio-activity concept Being applied to the clinic
Location of Implant Treatment Technology -------------- ★ ---------------- Dental implant
Location of evaluation technology ----------- ★ -------------------

1 is a scanning electron micrograph of a metal surface chemically treated for bioactive coating (a) process time 6 hours, b) process time 12 hours, c) process time 24 hours, d) process time 48 time)

Figure 2 is a contact angle photograph when the water droplets dropped on the metal specimen before the metal surface treatment according to the present invention.

Figure 3 is a contact angle photograph when the water droplets dropped on the metal surface treated metal specimen according to the present invention.

Figure 4 is a photograph of a Ledermann implant surface-treated by blasting method and acid corrosion.

Figure 5 is a photograph comparing the surface state before and after acid treatment after blasting.

Figure 6 is a surface photograph of titanium surface-treated with a laser.

Claims (6)

(a) surface treating titanium with an aqueous alkali solution of sodium hydroxide, (b) annealing the surface treated titanium, (c) impregnating the annealed titanium in a buffer containing a bioactive organic material to coat the bioactive organic material on the annealed titanium, and (d) a titanium surface treatment method comprising the step of drying the titanium coated with the bioactive organic material under reduced pressure; The surface treatment step is performed by etching the titanium in the aqueous sodium hydroxide alkali solution at a concentration of 5 mol / L at 600 ° C. for 6 hours; The annealing step is performed at an oxygen containing atmosphere and at a temperature of 900 ° C .; The contact angle of the annealed titanium surface is 20 °; The bioactive organic material is a surface treatment method of a metal, characterized in that the peptide comprising an RGD (Arg-Gly-Asp) sequence. delete delete delete delete delete

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