Dental implants: Surface modifications

1) Introduction:

One of the most important factors responsible for implant success is its primary stability. Implant failures are most commonly associated with poor bone quality 1. Various properties if implant such as composition, surface topography, surface roughness and surface energy affect the stability of implant tissue interface 2-4. Albrektsson et al. 5 (1981) recognized initially that the implant surface properties including topography, chemistry, surface charge, and wettability, are important factors influencing osseointegration. It has been suggested that surface topography may affect the amount of bone formed at the interface 6. Enhancing bone growth towards the implant surface has been regarded essential in cases with poor bone quality. Many in vivo studies have demonstrated that increased surface topography results in increased bone-to implant contact early after implant placement 7-11. Also it has been shown that after loading there are more implant failures in implants with relatively smooth surfaces 12-16, in comparison with rough-surfaced implants 17-19.  Implant surface modifications are also required because of immediate loading implants are subjected to biomechanically challenging situations. It has also been suggested that texturing the implant surface may not directly contribute to initial implant stability but it may reduce the risk of stability loss and consequently facilitating wound healing (secondary osseointegration) 20,21. Our goals of implant surface modifications are,

  • To achieve initial stability that would improve the tolerance of micro movements by implant and minimize the waiting-period required for loading the implant.
  • To provide a surface where the blood clot is stable and retained favouring the healing process.
  • To incorporate design factors, that would diminish the effect of shear forces on the interface (such as surface roughness related and thread features), so that marginal bone is preserved.
  • To design features that may stimulate bone formation, and/ or facilitate bone healing (secondary osseointegration).

The bioinert materials may behave differently when place in bone. Following terms should be known to us before we discuss the surface modifications of dental implants,

A) Osteogenesis:

It refers to the formation and development of bony tissue.

B) Osteoinduction:

Osteoinduction is the process by which osteogenesis is induced. In this case primitive, undifferentiated and pluripotent cells are stimulated to develop into the bone-forming cell lineage leading to formation of new bone.

C) Osteocunduction:

An osteoconductive surface is one that permits bone growth on its surface. In this case growth of bony tissue into the structure of an implant or a graft takes place.

2) Components of surface topography:

The topography of a surface can be divided into three different categories: form, waviness and roughness depending on the wavelength or peak-to-peak spacing of the surface features 22. Conventionally, the waviness and form are removed by filtering and numerical surface parameters are often calculated on the roughness alone and are thereafter called surface roughness parameters 23. The surface roughness parameters either describe surface characteristics in two dimensions, 2D (marked by R), or in three dimensions, 3D (marked by S).

Depending on what surface characteristics they are describing, 3D surface roughness parameters are divided into different groups which are 24-26,

  1. Amplitude
  2. Spatial
  3. Hybrid
  4. Volume and area
  5. Functional parameters

Amplitude refers to the amplitude property of the topographical features which are considered to be the most important property of the surface 25. Spatial parameters describe the texture, randomness, and periodicity of the surface. Hybrid parameters are combinations of spatial and amplitude parameters where a change in either of the two properties affects the value of the hybrid parameter. The volume and area parameters are defined from the bearing curve of the surface and describe the bearing and void property of the topography. Functional parameters are more specific parameters which describe particular characteristics of a surface such as fluid retention and bearing 26, 27. In simpler terms, three-dimensional parameters for surface roughness is average surface roughness (Sa) which represents the arithmetic mean of deviations in roughness from the mean plane of analysis. Surfaces with Sa between 1 and 2 μm are included in the” moderately rough surfaces”.’ Surfaces with Sa greater than 2 μm are “rough” surfaces 28.

In general terms implant surface roughness is divided, depending on the dimension of the measured surface features into macro, micro, and nano-roughness.

A) Macro roughness

It is defined as being in the range of millimeters to tens of microns. This scale directly relates to implant geometry, with threaded screw and macro porous surface treatments. Macro roughness can improve implant fixation and long-term mechanical stability of the implant. It is because of enhanced mechanical interlocking between the macro rough features of the implant surface and the surrounding bone 29,30.

B) Micro roughness

It is defined as being in the range of 1–10 μm. This is the ideal range which maximizes the interlocking between implant surfaces and surrounding bone. Studies supported by some clinical evidence suggest that the micron-level surface topography results in greater accrual of bone at the implant surface 30,31.

C) Nanoscale topographies

These have been introduced recently involving materials that have a nano-sized topography or are composed of nano-sized materials with a size range between 1 and 100 nm. Studies have shown that nanometer roughness plays an important role in the adsorption of proteins, adhesion of osteoblastic cells and thus the rate of osseointegration 32.

3) Role of surface energy and surface charge:

Surface energy is an important factor involved in the regulation of osteogenesis. The surface energy of a biomaterial is determined by the material’s surface-charge density and the net polarity of the charge. It has been said that depending on the surface energy, the surface state can either be hydrophilic or hydrophobic 33. Surface wettability is largely dependent on surface energy and influences the degree of contact with the physiological environment 34,35. In general, increase in the surface energy causes increase in the wettability of the surface thereby improving its biological activity. The energy state of the implant depends on the type of biomaterial, the handling during manufacturing, the mode of cleaning, sterilization, and needless to say, the handling of the implant during surgical procedure 36, 37. Surface charge plays an important role during initial biological reaction on the implant surface. In general, when the surface is positively charged, the surface turns hydrophilic and some of the plasma proteins essential for the initial osteogenic interactions adsorb to hydrophilic surfaces 38-40. However, contradicting results have been found in other studies in which it was found that on a negatively charged biomaterial surface, cells proliferate more actively; meanwhile, multiple layers of cells and enlarged colonies of osteoblast-like cells were also observed. In contrast, cell adhesion and proliferation on positively charged biomaterial were found to be subdued 41. Based on these findings, it has been hypothesised that a negatively charged surface is essential to obtain a bioactive material with good osseointegration properties 42

The surface charge of the implant can be modified by oxidization 43, chemical and topographical modification 44, 45, and by plasma treatment 46, 47.

At the nanoscale, a more textured surface topography increases the surface energy which in turn increases the wettability of the surface to blood, adhesion of cells to the surface, and facilitates binding of fibrin, matrix proteins, growth and differentiation factors. Therefore, nanotopography  by modulating cell behavior, can influence the process of cell migration, proliferation, and differentiation. These surfaces thus enhance the process of osseointegration by hastening the wound healing following implant placement 48.

4) Implant surface modification techniques:

On an implant surface, irregularities can be produced by two methods: ablative/subtractive procedures or additive procedures.

Various ablative and additive procedures for implant surface modifications

Ablative procedures

Additive procedures

Surface blasting

Acid etching

Anodic oxidation

Shot/laser peening

Plasma spraying

Electrophoretic deposition

Sputter deposition

Sol gel coating

Pulsed laser deposition

Biomimetic precipitation


A) Ablative procedures:

These are surface subtractive procedures where the implant is subjected various physical and chemical agents which make the implant surface rough by removing the implant biomaterial from its surface. These are as follows,

a) Surface blasting:

One of the most frequently used treatments for creating a rougher surface on a titanium dental implant is surface-blasting. Within the surface blasting there are 2 main groups: those created by grit blasting, such as aluminium oxide or titanium oxide and those using calcium phosphate as a resorbable blast media (RBM). The latter method creates a textured surface by blasting a traditional machined titanium implant with calcium phosphate ceramic, which is then passivated without acid etching to remove residual media

Grit blasting consists on bombarding a surface with small hard and biologically-inert ceramic particles, like alumina (Al2O3) or silicon carbide (SiC), titanium oxide and calcium phosphate 49, 50. Compressed air is used to project the particles through a nozzle at a very high velocity; depending upon size of the particles. There are some basic requirements of the blasting material which include: it should be chemically stable, should not affect the osseointegration property of implant and should be biocompatible.

The roughness values produced with the grit blasting technique depend mostly on the size of the particles used. A titanium surface grit-blasted with 600 μm alumina particles has a mean surface roughness of 4 μm and improves osteoblast cell response 51. However, it has been shown in studies that presence of particle remnants on the implant surface, even after a thorough cleaning, may influence detrimentally the physico-chemical properties of the surface 52, 53. The problem with alumina particles is that they often remain embedded on the implant surface and their residues are present even after ultrasonic cleaning, acid passivation and sterilization. Also, alumina is insoluble in acids. So, these factors adversely affect implant integration with bone. Titanium oxide particles which have average size of 25 μm produce surface roughness in the range of 1-2 μm.

Other media used for grit blasting include calcium phosphates such as hydroxyappatite (HA), β-tricalcium phosphate and their mixtures. These materials have particle size in the range of 75-85 μm 54 and most importantly they are restorable, biocompatible and osteoconductive which enhances the implant osseointegration properties.

b) Acid etching:

One of the most important advantages of acid etching is that it produces a highly clean and detailed surface, free of surface impurities and entrapped surface material. Studies have shown an enhanced bone apposition response around acid etched implants during healing 55. This procedure has been shown to greatly enhance implant osseointegration especially in early stages of peri-implant bone healing  56.

We also have a dual etching procedure where implant surface is subjected to application of hydrochloric and sulphuric acid. Small peaks and valleys are formed in a uniform pattern with a peak to peak distance of 1-3 μm and peak to valley distance of 5-8 μm 57. Osseotite (3i/implant innovations, west palm beach,FL) is commercially available dual etched implant.

Know more………

Sandblasted, large-grit, acid-etched (SLA) implants:

Implant surface has also been modified by the combination of grit blasting and acid etching procedure. These implants are referred to as sandblasted, large-grit, acid-etched (SLA) implants. The micro-roughened surface of sandblasted, large-grit, acid-etched (SLA) implants have been shown to have even better early osseointegration. Animal studies have shown mean bone–implant contact of 30%–40% for titanium plasma sprayed (TPS) implants as compared to 50%–60% for SLA implants 58. In a study done on TPS and SLA implants it has been shown that as compared to TPS implants, SLA implants were associated with significantly less bone loss, measured radiographically, before and 3 months after loading, a difference that persisted for at least 1 year after loading 59. Histological studies confirmed these results showing the percentage of bone–implant contact after 3 and 15 months of healing was significantly greater for SLA implants than for TPS implants 60. It was also shown that SLA implants has more favourable clinical outcomes during early loading (6 weeks after implant placement) 61-66.

c) Anodic oxidation:

Anodic oxidation is an electrochemical process that increases the TiO2 surface layer and roughness. Here, micro- or nanoporous surfaces is produced by potentiostatic or galvanostatic anodization of titanium in strong acids (H2SO4. H3PO4, HNO3, HF) at high current density (200 A/m2) or potential (100 V). The result of the anodization is to thicken the oxide layer to more than 1,000 nm on titanium. When implant is immersed any of the above electrolyte, it becomes an anode in an electrochemical cell.  When a potential is applied to the sample, ionic transport of charge transfers through the cell, and an electrolytic reaction takes place at the anode, resulting in the growth of an oxide film. Surface roughness of the TiUnite implant increases from 1 to 2 μm (peak-to-valley distance) at the coronal part to 7 to 10 μm at the apical part 67. The TiUnite dental implant (Branemark System, Nobel Biocare USA, Yorba Linda, CA) is an anodized commercially pure titanium dental implant.

d) Shot/laser peening:

In this process the implant surface is bombarded with small spherical media called shot. Each piece of shot striking the material acts as a tiny hammer, imparting to the surface small indentations or dimples. In order to create a dimple on the surface, the surface fibers of the material must be yielded in tension. Below the surface, the fibers try to restore the surface to its original shape, thereby producing below the dimple a hemisphere of cold-worked material highly stressed in compression 68. In this procedure a honeycomb like uniform surface with small pores is achieved.

Recently laser peening method has been introduced which is a non-contact, no-media, and contamination-free peening method 69. Laser peening drives a high amplitude shock wave into a material surface using a high energy pulsed laser. The effect on the material being processed is achieved through the mechanical “cold working” effect produced by the shock wave, not a thermal effect from heating of the surface by the laser beam.

Before the treatment, the surface is covered by a protective ablative layer (paint or tape) and a thin layer of water. After this a high-intensity (5-15 GW/cm2) nanosecond pulses (10-30 ns) of laser light beam (3-5 mm width) striking the ablative layer generate a short-lived plasma which causes a shock wave to travel into the implant surface. This shock wave induces the compressive residual stresses which when released produce a dimple leading to formation of rough surface on repeated application of laser beam. It also causes improvements in fatigue life and retarding in stress corrosion cracking occurrence 70-72.

B) Additive procedures:

In these procedures the implant surface is coated with various biomaterials which improve the biological and bio-mechanical properties of implants. The implant surface is coated with calcium phosphates mainly hydroxyappatite (HA). When the implant is placed in bone, the release of calcium and phosphate in the surrounding tissue increases the saturation of the ions in the tissue fluid causing precipitation of biological apatite onto the surface of implant.  

a) Plasma spraying:

This technique is based on thermal spray technology which uses a device to melt and coating material at a high velocity onto the substrate 73. The plasma spray method has been widely accepted as the apatite coating method because it gives tight adhesion between the apatite coating and Ti. Plasma-sprayed HA coatings on commercial dental implants consist of mixtures of calcium phosphate phases, predominantly a crystalline calcium phosphate phase, hydroxyapatite, and an amorphous calcium phosphate with varying ratios. Hydroxyapatite is a major mineral component in animal and human bodies and has been widely as a biomedical implant material. Spherical HA ceramic beads have recently been developed that show improvements in mechanical properties and physical and chemical stability. These spherical ceramic beads are typically 20-80µm in size.

Commercially available plasma spray coating has been reported to have a thickness of greater than 30 μm. The major advantages of this technique are its simplicity, rapid deposition rate, low substrate temperature, low cost and variable coating porosity. However, studies have shown loss of HA coating from surface of implants with due course of time after implant placement 74. There are two points to be remembered about HA coatings: First, HA would tend to fuse better to the bone than to the implant itself, and with high occlusal loads (excessive biting forces in some individuals/sites in the mouth), the HA would break off of the implant. Secondly, HA coating is very susceptible to penetration by dental plaque, consisting of oral bacteria and their endotoxins. If the roughened HA surface of a dental implant becomes exposed due to some initial or peri-implantitis bone loss, the tendency is for further bone loss to occur because the implant surface could not be adequately cleaned or decontaminated, leading to more inflammation and eventually greater bone loss.

Various implant surface modifications have been studied for their bone-implant contact. One study reported that highest extent of bone-implant interface was observed in sand-blasted and acid etched surfaces (large grit; HCl/H2SO4) with mean values of 50-60%, and hydroxyapatite (HA)-coated implants with 60-70%. It was minimum for electropolished, as well as the sand-blasted and acid pickled (medium grit, HF/HNO3) implant surfaces with mean values ranging between 20 and 25%. For sand-blasted implants, with a large grit, and titanium plasma-sprayed implants the mean bone contact was 30-40% 75.  

So, it was suggested that sand-blasting and chemical etching with HCl/ H2SO4 as well as HA coating, seemed to be the most promising alternatives to titanium implants with smooth or titanium plasma-sprayed surfaces 75. The advantages of plasma spray method are, it is widely accepted as a apatite coating method because it gives tight adhesion between the apatite coating and Ti. The disadvantage of this method is the requirement of extremely high temperatures (10,000-12,000 °C) during the coating process. Unfortunately, it results in potentially serious problems including

  1. An alteration of structure.
  2. Formation of apatite with extremely high crystallinity.
  3. Long term dissolution and the accompanying debonding of the coating layer.

To overcome these drawbacks methods like sol-gel coating have been developed.

b) Titanium plasma spray coating

Coating of pure titanium coatings on Ti-6Al-4V alloy have been used in order to improve the biocompatibility of functional titanium-based alloys. These coatings are believed to favour the osseointegration of the bone because of the inherent roughness of such coatings, although they do not induce osteogenesis per se.

c) Radio frequency (RF) magnetron sputtering:

Radio frequency (RF) magnetron sputtering is a recent technique used in modification of implant surface. The application of magnetron sputtering offers a flexible approach to surface improvement of metal implants. This technique facilitates to producing of dense and well-adhered films with controlled elemental composition 76.

In this technique, magnetic field is created by permanent magnets, electromagnets or a combination of both. This configuration acts to trap electrons. Thus, in a magnetron sputtering discharge, atoms are sputtered from the cathode target by magnetically confined plasma 77. The target material is sputtered by the bombardment of high energy ions accelerated over the cathode sheath potential. Secondary electrons are emitted and accelerated away from the target surface as a result of the ion bombardment. These electrons play an important role in maintaining the plasma. A magnetic field confines the ionizing energetic electrons near the cathode allowing operation at high plasma densities and low pressures.

d) Electrophoretic deposition (EPD):

Electrophoretic deposition (EPD) is a special colloidal processing technique that uses the electrophoresis mechanism for the movement of charged particles suspended in a solution under an electric field, to deposit them in an ordered manner on a substrate to develop thin and thick films, coatings and free-standing bodies 78-80. EPD is usually carried out in a two-electrode cell. The motion of charged particles dispersed in a liquid towards the working electrode is achieved by electrophoresis, and the solid deposit formation and growth on the electrode occur primarily via particle coagulation 81. Compared with other particle-processing methods, EPD is able to produce uniform deposits (coatings) with high microstructural homogeneity, to provide adequate control of coating thickness and to deposit thin and thick films on substrates of different shapes and on three-dimensional complex and porous structures 82.

The disadvantage of this treatment is the requirement of post-deposition heat treatment to densify the coating. In case of hydroxyapatite (HA) coating the feedstocks requires the temperature of at least 1200⁰C to be densified. Another problem is, temperatures above 1050°C affect the oxide layer and mechanical properties of a stainless steel or titanium alloy as well as decompose HA affecting the interfacial strength between the metal and coating.

e) Sol-gel coating:

The sol-gel process is based on the hydrolysis and condensation of bioactive material on implant surface. In comparison to plasma spray method, the sol–gel technique offers certain advantages. Because of the high chemical homogeneity, fine grain structure and low crystallization temperature of the resultant coating is achieved. As compared to plasma coating it is both an economical and technically simple procedure to perform. Bioactive glass (BG) composites also have been used to coat implant surface by this method. This method has also been used to deposit TiO2 layer on implant surface. The sol-gel-derived HA and TiO2 films, with thicknesses of about 800 and 200 nm, adhered tightly to each other and to the CpTi (grade 2) substrate.

f) Pulsed laser deposition (PLD):

Pulsed laser deposition (PLD) has been used to deposit hydroxyapatite (HA) ceramic over titanium substrate with an interlayer of titania. PLD is an alternative method to coat metal substrates (such as implant surface) with HA in order to improve both the chemical homogeneity and the mechanical properties of calcium phosphate coatings 83. PLD has successfully produced HA coatings with various compositions and crystallinity 84. Moreover, PLD can synthesize thin HA coatings, adequate for high fatigue resistance.

g) Biomimetic precipitation:

The term Biomimetic refers to biomaterial having the ability to induce differentiation of the appropriate cells (i.e., endothelial and osteoblastic cells) for the formation of new bone; it should be easily synthesized or produced, rather than having to be extracted from allograft materials (to eliminate all risks of disease transmission); it should be easily and quickly resorbed as the osteogenic response occurs; it should have no immune-provoking properties; it should be easily transported and stored; and it should be reasonably cost-effective 85. The incorporation of recombinant bone morphogenetic proteins (BMPs), which are produced by genetic engineering onto the implant surface, is the future of implant surface modifications. These methods are presently under research. Because these methods are done at molecular levels, the evolution of mechanisms to make these techniques biologically efficient and economically acceptable is a major task in this direction.

Various commercially available implants and their surface modifications

Commercially available implant

Surface modification

Nobel Active: (TiUnite) Nobel Biocare, Zurich. Switzerland Anodic oxidation. Phosphate enriched titanium oxide
Ankylos Plus. XiVE. Frialit: Dentsply,  Friadent. GmbH Sandblasted, large grit blasted, acid-etched.
Leader italia: Traditional implant line Biological Organic Acid Treatment
Leader italia: TiXos Line. Laser Sintered Titanium
Tioblast: AstraTech Dental. Molndal. Sweden Grit blasted with titanium oxide
Zimmer Screw Vent Microtextured hydroxyapatite surface
Laserlok Surface—Biohorizon. Birmingham, Alabama Laser peening
Adin implant system Titanium plasma sprayed
Adin implant system. OsseoFixâ„¢ calcium phosphate biocompatible resorbable blast media (RBM)
Straumann Bone Level: Institut.  Straumann AG, Switzerland SL Active: Sandblasted. large grit blasted followed by acid etching
NanoTite: Biomet 3i, Palm Beach Gardens. Florida. USA Calcium phosphate by discrete crystal deposition.
GSIII: Osstem. South Korea Resorbable blast media (RBM): Calcium phosphate hydroxyapatite
3i/implant innovations (Osseotite), west palm beach, FL. Dual etching

5) Future trends:

Chemical modification of the titanium oxide layer on implant surface for more favourable biological response is under extensive research. Various methods have been employed for this purpose which includes treatment in simulated body fluid 86, covalent attachment of biological molecules 87, changes in the surface ion content 88, glow discharge 89, or alkali treatment 90. It has been demonstrated that these modifications alter the cellular response during healing after implant placement.

A) Chemical modification by fluorides:

Fluoride has specific attraction for calcium and phosphates and the known beneficial effects of clinical importance that can be observed when this ion is in contact with calcified tissues 91, 92 . It has been shown that the trabecular bone density is increased and calcification of bone is induced when fluoride is present during bone remodelling 93, 94. Using radioactively labeled phosphorous, 32P, it has been shown that uptake of phosphate is significantly higher at the fluoride-modified implant surfaces than at the non-modified titanium dioxide surfaces demonstrated by an elevated level of radioactivity at these surfaces 95.

Fluorides also seem to induce bone cell growth factors which are required during osteogenesis 96. Fluoride is suggested to have an action on osteoprogenitor cells and undifferentiated osteoblasts. Because of these reasons the fluoride-modified titanium dioxide has modified surface properties in reaction with calcium phosphates compared with non-modified titanium dioxide. Animal experiments have reported that the fluoridated, blasted implants have a significantly higher removal torque than the blasted test implant, again indicative of a bioactive reaction of fluoridated Ti implants 97.

Low concentration of hydrogen fluoride has been used on titanium dioxide without changing the surface microtexture of implant significantly. Small amounts of fluoride will then be incorporated into the crystal structure of the titanium dioxide. Further research is going on this direction to better understand the role of fluoride and its use in implant dentistry.

B) Use of bis-phosphonates:

Bisphosphonates all have in common the P–C–P structure, which is similar to the P–O–P structure of native pyrophosphate. These agents inhibit osteoclastic bone resorption of the bone. Bisphosphonates attach to hydroxyapatite binding sites on bony surfaces, especially surfaces undergoing active resorption. When osteoclasts begin to resorb bone that is impregnated with bisphosphonate, the bisphosphonate released during resorption impairs the ability of the osteoclasts to form the ruffled border, to adhere to the bony surface, and to produce the protons necessary for continued bone resorption. Detailed description of mechanism of action of these drugs is available in “Host Response Therapeutics for Periodontal Diseases”.

Research work has shown significant increase in Bone-implant contact when the implant surface was coated with pamidronate or zoledronate.  The clinical application of these agents incorporated on implant surface is still awaited.

C) Use of growth factors:

Many studies have been done to investigate the effect of different growth factors on peri-implant osseointegration 98-103. Most important of them are the BMP’s which belong to TGF-β superfamily. These proteins control both cell growth and differentiation, according to cell type and state of differentiation 104, and also directly affect expression of receptors involved in surface recognition and cellular attachment to titanium implants 105. Unfortunately, most of the research done on incorporation of BMP’s on implant surface has not so far reached the clinical practice. Reason for this problem is that growth factors are by nature free-floating, short-lived signals that initiate or modulate small, incremental changes in cells as part of cascade reactions. Another factor that should be kept in mind is that the effect of these signals varies dramatically with cell-type, stage, and location, with the condition of the surrounding tissues, and with the presence of other growth factors.

D) Tissue engineering:

Tissue engineering is the use of a combination of cells, engineering materials, and suitable biochemical factors to improve or replace biological functions 106. It is an interdisciplinary approach where the principles of engineering and life sciences are combined toward the development of biological substitutes that restore, maintain, or improve tissue function. It involves the interaction of cells with a material surface where behaviour of the cells is studied. For example osteoblasts and chondrocytes are sensitive to subtle differences in surface roughness and surface chemistry.

Clinically a tissue engineered Scaffold material is used to carry the bio active molecules. This scaffold acts as artificial extracellular matrices (ECM) and as a spacer keeping a certain open space 107. When placed in body scaffold material has to be dissolved completely into the living body after auto-cell is regenerated with artificial extracellular matrices 108. Various materials have been utilized to be used as scaffold which include blended-polymer scaffolds, collagen-based scaffolds, and composite scaffolds of polyhydroxybutyrate-polyhydroxyvalerate with bioactive wollastonite (CaSiO3) 109. A three-dimensional printing (3DP) technology can be used to fabricate porous scaffolds which can be supplemented with bone morphogenetic proteins (BMPs).

Electrospinning is another method by which scaffolds made from the synthetic and natural polymers 110. Research work is going on in this field to make these complicated procedures easy and clinically applicable. In future we have to do more research in this field to find out the clinical applications and drawbacks of these techniques.

6) Conclusion:

The long term stability and functionality of dental implants is our ultimate goal.  Surface modifications of dental implant play important role in this endeavour. Adding bioactive surface layers to implants could improve implant biocompatibility, osseointegration, and durability, all important qualities required for long-term performance. Present research is focused on identifying the bio-molecule carriers which can transport the bio-molecules like bone morphogenetic proteins in active form during implant placement and promote initial healing and bone formation. It should be noted that the implant first comes in contact with fluid (blood) during placement, which is a major factor for initial cell recruitment onto the implant surface. Recruiting growth factor-producing cells to the bone–implant interface through focal attachment and molecular recognition may help in faster bone formation. Although every effort has been made to gather all the information presently available, due to massive research going on in this field frequently new researches are coming up. Present article shall be updated with all the new information as and when available in future. 


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