Fig. 8. EDS 5 min
Fig. 8. EDS 5 min
Fig. 7. EDS 3 min
Fig. 7. EDS 3 min
Fig. 6. EDS 1 min
Fig. 6. EDS 1 min
Fig. 5. EDS control
Fig. 5. EDS control
Fig. 4. Group 4—5 min
Fig. 4. Group 4—5 min
Fig. 3. Group 3—3 min
Fig. 3. Group 3—3 min
Fig. 2. Group 2—1 min
Fig. 2. Group 2—1 min
Fig. 1. Group control
Fig. 1. Group control
Element
Weight %
Atoms %
Carbon
15.07
26.19
...
Element
Weight %
Atoms %
Carbon
10.43
23.42
...
Element
Weight %
Atoms %
Carbon
4.12
15.29
...
Element
Weight %
Atoms %
Carbon
4.79
18.86
...
Element
Weight %
Atoms %
Carbon
8.54
31.34
...
Element
Weight %
Atoms %
Carbon
4.47
19.93
...
Element
Weight %
Atoms %
Carbon
8.02
38.2
...
Element
Weight %
Atoms %
Carbon
8.22
37.21
...
Groups
Plasma electrolytic oxidation—time (min)
Voltage (V)
Current (A)
1
–
–
2
1
ΔU = 160 to 200 V
≅0.18
3
3
ΔU = 160 to 280 V
≅0.19
4
5
ΔU = 160 to 300 V
≅0.18
Table 1 Distribution of groups
Goularte, M.A.P.C., Barbosa, G.F., da Cruz, N.C. et al. Achieving surface chemical and morphologic alterations on tantalum by plasma electrolytic oxidation.
Int J Implant Dent 2, 12 (2016). https://doi.org/10.1186/s40729-016-0046-2
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Received: 18 November 2015
Accepted: 12 April 2016
Published: 16 April 2016
DOI: https://doi.org/10.1186/s40729-016-0046-2
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were m...
The authors declare that they have no competing interests.
MAPCG contributed to the concept/design, data collection, data analysis/interpretation, drafting of the article, critical revision of the article, and approval of the article. GFB carried out the data analysis/interpretation, drafting of the article, critical revision of the article, and approval of the article. NCC contributed to the dat...
Department of Prosthodontics, Implantology Pontifical Catholic University of Rio Grande do Sul - PUCRS, Av. Ipiranga, 6681 Prédio 06, Partenon, CEP: 90619-900, Porto Alegre, RS, Brazil
Marcelo Augusto Pinto Cardoso Goularte
Clinical Department, Universidade Luterana do Brasil - Torres (ULBRA-TORRES), Rua Universitária, 1900, Parque do Balonismo, CEP 95560-000, Torres, RS, Brazil
Gustavo Frain...
Yerokhin AL, Nie X, Leyland A, Matthews A, Dowey SJ. Plasma electrolysis for surface engineering. Surf Coat Technol. 1999;122(2-3):73–93. doi:10.1016/S0257-8972(99)00441-7.
Hosoki M, Nishigawa K, Miyamoto Y, Ohe G, Matsuka Y. Allergic contact dermatitis caused by titanium screws and dental implants. J Prosthodont Res. 2016. doi: 10.1016/j.jpor.2015.12.004. [Epub ahead of print].
Goutam M, Giri...
Gittens RA, Olivares-Navarrete R, Cheng A, Anderson DM, McLachlan T, Stephan I, et al. The roles of titanium surface micro/nanotopography and wettability on the differential response of human osteoblast lineage cells. Acta Biomater. 2013;9(4):6268–77. doi:10.1016/j.actbio.2012.12.002. Epub 2012 Dec 8.
Bauer S, Schmuki P, von der Mark K, et al. Engineering biocompatible implant surfaces part I: ...
Thus, this study has examined the possibility of activating an alteration surface in tantalum using the anodizing process, which is effective in other metals like titanium. From our findings, it was possible to develop time exposure protocols in order to obtain conductive surface alterations similar to those already available from some of the largest manufacturers of oral implants. Scanning electr...
The search for new biomaterials and biocompatible metals has always been a common objective of human rehabilitation research centers. In implant dentistry, titanium has successfully established itself as the material of choice for dental implants. However, several studies have reported cases of metal allergy caused by titanium-containing materials [15–17] and some immune dysfunctions in certain ...
Tables 2 and 3 show similar rates among the chemical elements present on the non-treated tantalum surface—group 1 (Fig. 5). In Tables 4 and 5 (group 2), calcium (Ca) is included. The rates for the other chemical elements are similar to the rates in group 1 (Fig. 6). In Tables 6 and 7, group 3 sample shows the basic chemicals present in previous groups and similar rates (Fig. 7). Two chemic...
The analysis of the images obtained by scanning electron microscopy confirmed the changes on the surface of tantalum strips according to different exposure times. In Fig. 1, we can observe Ta surface with grooves resulting from the machining of the metal with no surface treatment. As the magnitude increases, the image shows the lines pattern with its peculiar characteristics from the manufacturin...
Within a 50-mL tank, the electrolytic solution as described above received a voltage variation of 160 V initial tension at zero time and a final tension at the preset end-time for each group of samples. There was a gradual increase in voltage due to the maintenance of a fairly constant current at around 0.15 to 0.25 A. The electrolytic solution was periodically changed to prevent solution satura...
We used 60 strip-shaped samples of tantalum with the following dimensions: 7 mm wide, 11 mm long, and 0.01 mm thick (Kurt J. Lesker Company—USA, 99.95 % purity). The samples were washed in distilled water and placed in an ultrasonic tank containing acetone (Ultra Sonic-1440 Plus—Odontobrás, Ribeirão Preto/SP, Brazil) to remove residues. Then, they were divided into four groups: in group ...
In this way and following the successful results already obtained with Titanium, this study aimed to develop an oxidized surface layer on Tantalum samples and, subsequently, analyze the samples’ topography and levels of salt deposition using an electronic microscope.
The use of materials that come into direct contact with human tissues such as the bone requires maximum biological security. These materials remain for a long period of time or even indefinitely in the human body, and no negative reactions, like toxicity or carcinogenic effects, shall be acceptable.
For this reason, biocompatibility of new materials has been widely studied, and only after a lot o...
Search for materials that may either replace titanium dental implants or constitute an alternative as a new dental implant material has been widely studied. As well, the search for optimum biocompatible metal surfaces remains crucial. So, the aim of this work is to develop an oxidized surface layer on tantalum using plasma electrolytic oxidation (PEO) similar to those existing on oral implants bee...
Fig. 5. Osteoblasts with an orientation tendency after 24 h of rotation (phallacidin fluorescence staining). On the left side with 200× and on the right side with 400× magnification. The yellow arrows show the orientation of the cells. The red arched arrow within the coloured circle shows the direction of rotation. The dashed white line oriented to the right stands for the resulting centrifug...
Fig. 4. Randomly orientated osteoblasts without influence of rotation (phallacidin fluorescence staining). On the left side with 200× and on the right side with 400× magnification. The white X on the coloured circle marks the location upon the plate where the osteoblasts were located. The red X marks the centre of the plate
Fig. 4. Randomly orientated osteoblasts without influence of rotati...
centrifugal force and the glass plates’ dimensions. For example, at a distance of 25 mm from the centre of the upper plate, the shear forces’ value is 8.33 dyn/cm2, together with an additional centrifugal force that has a value of 0.55 dyn/cm2
Fig. 3. Diagram for visualisation of the calculation of shear stress rates taking into account the centrifugal force and the glass plates’ dim...
earing gap and bottom plate are shown on the left side; rotation speed = 200 rpm; colour code bar (left edge) showing shear force values [Pa] [1 Pa = 10 dyn/cm2]; flow direction presented by arrows
Fig. 2. Side view of a computerized simulation, showing the flow chambers’ lower compartment and the flow profile in between the two plates; shearing gap and bottom plate are shown on ...
Fig. 1. Three-dimensional illustration (a–e) and photography (f) of the experimental setup with the components marked numerical. a as the lower plate); 2 Rotating glass panel [60 mm diameter (cell bearing)]; 3 Titanium axis. b4 Liquid medium (red). cGearwheel with set screw. eng ring with additional set screw
Fig. 1. Three-dimensional illustration (a–e) and photography (f) of the experim...
Culture medium/additives
Manufacturer
Order no.
Concentration
Dulbecco’s modified Eagle medium (DMEM) with l-glutamine, plus 4.5 g glucose,...
Component
Manufacturer
Order no.
Large petri dish
Becton Dickinson, Franklin Lakes, NJ, USA
...
Kämmerer, P.W., Thiem, D.G.E., Alshihri, A. et al. Cellular fluid shear stress on implant surfaces—establishment of a novel experimental set up.
Int J Implant Dent 3, 22 (2017). https://doi.org/10.1186/s40729-017-0085-3
Download citation
Received: 27 February 2017
Accepted: 22 May 2017
Published: 31 May 2017
DOI: https://doi.org/10.1186/s40729-017-0085-3
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were...
Correspondence to
D. G. E. Thiem.
Department of Oral and Maxillofacial Surgery, Facial Plastic Surgery, University Medical Centre Rostock, Schillingallee 35, 18057, Rostock, Germany
P. W. Kämmerer & D. G. E. Thiem
Department of Prosthetic and Biomaterial Sciences, King Saud University, Riyadh, Saudi Arabia
A. Alshihri
Harvard School of Dental Medicine, Boston, MA, USA
A. Alshihri
Department of Oral and Maxillofacial Surge...
The authors thank the Department of Hydraulic Machines, Faculty of Mechanical Engineering, Technical University of Munich, Germany, for helping with the computerised simulations.
Nothing to declare
The datasets supporting the conclusions of this article are available at the repository of the University Medical Centre Mainz, Germany, and can be provided on request.
PK had substantial contributio...
Papadaki M, Eskin SG. Effects of fluid shear stress on gene regulation of vascular cells. Biotechnol Prog. 1997;13(3):209–21.
James NL, Harrison DG, Nerem RM. Effects of shear on endothelial cell calcium in the presence and absence of ATP. FASEB J. 1995;9(10):968–73.
Kämmerer PW, Lehnert M, Al-Nawas B, Kumar VV, Hagmann S, Alshihri A, et al. Osseoconductivity of a specific streptavidin-biot...
Hughes-Fulford M. Signal transduction and mechanical stress. Sci STKE. 2004;2004(249):RE12.
Ruel J, Lemay J, Dumas G, Doillon C, Charara J. Development of a parallel plate flow chamber for studying cell behavior under pulsatile flow. ASAIO J. 1995;41(4):876–83.
Kazakidi A, Sherwin SJ, Weinberg PD. Effect of Reynolds number and flow division on patterns of haemodynamic wall shear stress near br...
Becker J, Kirsch A, Schwarz F, Chatzinikolaidou M, Rothamel D, Lekovic V, et al. Bone apposition to titanium implants biocoated with recombinant human bone morphogenetic protein-2 (rhBMP-2). A pilot study in dogs. Clin Oral Investig. 2006;10(3):217–24.
Hung CT, Allen FD, Pollack SR, Brighton CT. What is the role of the convective current density in the real-time calcium response of cultured bon...
Ehrlich PJ, Lanyon LE. Mechanical strain and bone cell function: a review. Osteoporos Int. 2002;13(9):688–700.
Vaughan TJ, Haugh MG, Mcnamara LM. A fluid-structure interaction model to characterize bone cell stimulation in parallel-plate flow chamber systems. J R Soc Interface. 2013;10(81):20120900.
Weinbaum S, Cowin SC, Zeng Y. A model for the excitation of osteocytes by mechanical loading-in...
To create fluid shear stress under in vitro conditions, several flow chambers have been developed in the past. The experimental setup of the flow chamber in the centre of this study offers advantages such as simplicity to assemble and ease of use as well as the creation of reproducible fluid shear forces on cells. Due to the new design, different cell types could be simultaneously analysed under r...
Besides, in the model reported in this study, microscopic examinations are possible after completing the experiment only. Nevertheless, an advantage of the new flow chamber is the possibility of testing different cell colonies simultaneously in one single experiment by placing cells in different radial locations on the spinning disc. Due to the current flow gradient from the centre to the peripher...
Due to the fact that constant flows were generated within the parallel flow chamber only, the situations of in vitro experiments differ from in vivo setting where dynamic flow profiles are particular [33]. As the constant laminar flow profile is not physiological in bones [34], vessels and other tissues [35], the informative value of the experimental setting is limited but it could be used for var...
The aim of this study was to establish a new FSS model that is easy to use as well as simple to assemble in order to create reproducible fluid shear forces on cells close to implant material surfaces. Todays’ commonly used commercial flow devices differ in geometry and function, which makes comparisons between experiments difficult [4, 10, 26, 27]. The benefits of this novel testing device are r...
in which ρ = density, h = height, ω = angular velocity and r = radius.
Figure 3 shows the respective physical force and its dependence on a bigger radius and higher rotational speed. The results of this study indicate that the centrifugal force represents only a little proportion of effective forces. Hence, the centrifugal forces’ impacts on the tested cells are considered to be insignifican...
Our analysis was focused on two main aspects:
Simulation of the fluid flow characteristics as well as quantification of the arising shear forces at the plate/plate flow chamber with reliable reproducibility
Assessment of the impact of fluid shear stress on osteoblast cells in terms of altered cell morphology and intracellular structural changes
The computational fluid dynamic analysis and the q...
For constant and fully developed laminar flow between the two parallel plates, the magnitude of the wall shear stress (τ) in between was calculated by formula 1:
in which η is the dynamic fluid viscosity (dyn/cm2), r is the radius of the plate (cm), ω stands for angular velocity and H for height (vertical distance in between the two plates).
To get information whether the flow is laminar or t...
A three-dimensional illustration and photography of the plate/plate flow chamber model is shown in Fig. 1. A detailed list of used parts can be found in Appendix 1.
The circulation within the flow chamber was generated by an externally attached electric motor, which rotates up to 500 rounds per minute (rpm). A commercial grade 4 pure medical titanium gear shaft (length = 40 mm, diameter =...
Therefore, the aim of the present study was to establish a new cell chamber model for FSS simulation and stimulation. In addition to its ease of use, the reported model in this study should meet the requirements of a simple design, generating reproducible flow characteristics next to laminar flows and clearly defined flow gradients on implant surfaces.
Cells can be influenced by different mechanostimuli, which lead to an activation of cellular and inter-cellular responses. These reactions may be caused by either a direct stimulation of the cell body (mechanoreception) or indirect cellular stimulation (response) [1,2,3]. Extracellular fluid movement induces fluid shear stress (FSS) that can result in different cellular processes including prolife...
Mechanostimuli of different cells can affect a wide array of cellular and inter-cellular biological processes responsible for dental implant healing. The purpose of this in vitro study was to establish a new test model to create a reproducible flow-induced fluid shear stress (FSS) of osteoblast cells on implant surfaces.
As FSS effects on osteoblasts are detectable at 10 dyn/cm2, a custom-made f...
Fig. 5. Osteoblasts with an orientation tendency after 24 h of rotation (phallacidin fluorescence staining). On the left side with 200× and on the right side with 400× magnification. The yellow arrows show the orientation of the cells. The red arched arrow within the coloured circle shows the direction of rotation. The dashed white line oriented to the right stands for the resulting centrifug...
Fig. 4. Randomly orientated osteoblasts without influence of rotation (phallacidin fluorescence staining). On the left side with 200× and on the right side with 400× magnification. The white X on the coloured circle marks the location upon the plate where the osteoblasts were located. The red X marks the centre of the plate
Fig. 4. Randomly orientated osteoblasts without influence of rotati...
to account the centrifugal force and the glass plates’ dimensions. For example, at a distance of 25 mm from the centre of the upper plate, the shear forces’ value is 8.33 dyn/cm2, together with an additional centrifugal force that has a value of 0.55 dyn/cm2
Fig. 3. Diagram for visualisation of the calculation of shear stress rates taking into account the centrifugal force and the glas...
e in between the two plates; shearing gap and bottom plate are shown on the left side; rotation speed = 200 rpm; colour code bar (left edge) showing shear force values [Pa] [1 Pa = 10 dyn/cm2]; flow direction presented by arrows
Fig. 2. Side view of a computerized simulation, showing the flow chambers’ lower compartment and the flow profile in between the two plates; shearing gap...
Fig. 1. Three-dimensional illustration (a–e) and photography (f) of the experimental setup with the components marked numerical. a lower plate); 2 Rotating glass panel [60 mm diameter (cell bearing)]; 3 Titanium axis. b4 Liquid medium (red). cwheel with set screw. e ring with additional set screw
Fig. 1. Three-dimensional illustration (a–e) and photography (f) of the experimental setup w...
Culture medium/additives
Manufacturer
Order no.
Concentration
Dulbecco’s modified Eagle medium (DMEM) with l-glutamine, plus 4.5 g glucose,...
Component
Manufacturer
Order no.
Large petri dish
Becton Dickinson, Franklin Lakes, NJ, USA
...
Kämmerer, P.W., Thiem, D.G.E., Alshihri, A. et al. Cellular fluid shear stress on implant surfaces—establishment of a novel experimental set up.
Int J Implant Dent 3, 22 (2017). https://doi.org/10.1186/s40729-017-0085-3
Download citation
Received: 27 February 2017
Accepted: 22 May 2017
Published: 31 May 2017
DOI: https://doi.org/10.1186/s40729-017-0085-3
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were...
Correspondence to
D. G. E. Thiem.
Department of Oral and Maxillofacial Surgery, Facial Plastic Surgery, University Medical Centre Rostock, Schillingallee 35, 18057, Rostock, Germany
P. W. Kämmerer & D. G. E. Thiem
Department of Prosthetic and Biomaterial Sciences, King Saud University, Riyadh, Saudi Arabia
A. Alshihri
Harvard School of Dental Medicine, Boston, MA, USA
A. Alshihri
Department of Oral and Maxillofacial Surge...
The authors thank the Department of Hydraulic Machines, Faculty of Mechanical Engineering, Technical University of Munich, Germany, for helping with the computerised simulations.
Nothing to declare
The datasets supporting the conclusions of this article are available at the repository of the University Medical Centre Mainz, Germany, and can be provided on request.
PK had substantial contributio...
Papadaki M, Eskin SG. Effects of fluid shear stress on gene regulation of vascular cells. Biotechnol Prog. 1997;13(3):209–21.
James NL, Harrison DG, Nerem RM. Effects of shear on endothelial cell calcium in the presence and absence of ATP. FASEB J. 1995;9(10):968–73.
Kämmerer PW, Lehnert M, Al-Nawas B, Kumar VV, Hagmann S, Alshihri A, et al. Osseoconductivity of a specific streptavidin-biot...
Hughes-Fulford M. Signal transduction and mechanical stress. Sci STKE. 2004;2004(249):RE12.
Ruel J, Lemay J, Dumas G, Doillon C, Charara J. Development of a parallel plate flow chamber for studying cell behavior under pulsatile flow. ASAIO J. 1995;41(4):876–83.
Kazakidi A, Sherwin SJ, Weinberg PD. Effect of Reynolds number and flow division on patterns of haemodynamic wall shear stress near br...
Becker J, Kirsch A, Schwarz F, Chatzinikolaidou M, Rothamel D, Lekovic V, et al. Bone apposition to titanium implants biocoated with recombinant human bone morphogenetic protein-2 (rhBMP-2). A pilot study in dogs. Clin Oral Investig. 2006;10(3):217–24.
Hung CT, Allen FD, Pollack SR, Brighton CT. What is the role of the convective current density in the real-time calcium response of cultured bon...
Ehrlich PJ, Lanyon LE. Mechanical strain and bone cell function: a review. Osteoporos Int. 2002;13(9):688–700.
Vaughan TJ, Haugh MG, Mcnamara LM. A fluid-structure interaction model to characterize bone cell stimulation in parallel-plate flow chamber systems. J R Soc Interface. 2013;10(81):20120900.
Weinbaum S, Cowin SC, Zeng Y. A model for the excitation of osteocytes by mechanical loading-in...
To create fluid shear stress under in vitro conditions, several flow chambers have been developed in the past. The experimental setup of the flow chamber in the centre of this study offers advantages such as simplicity to assemble and ease of use as well as the creation of reproducible fluid shear forces on cells. Due to the new design, different cell types could be simultaneously analysed under r...
Besides, in the model reported in this study, microscopic examinations are possible after completing the experiment only. Nevertheless, an advantage of the new flow chamber is the possibility of testing different cell colonies simultaneously in one single experiment by placing cells in different radial locations on the spinning disc. Due to the current flow gradient from the centre to the peripher...
Due to the fact that constant flows were generated within the parallel flow chamber only, the situations of in vitro experiments differ from in vivo setting where dynamic flow profiles are particular [33]. As the constant laminar flow profile is not physiological in bones [34], vessels and other tissues [35], the informative value of the experimental setting is limited but it could be used for var...
The aim of this study was to establish a new FSS model that is easy to use as well as simple to assemble in order to create reproducible fluid shear forces on cells close to implant material surfaces. Todays’ commonly used commercial flow devices differ in geometry and function, which makes comparisons between experiments difficult [4, 10, 26, 27]. The benefits of this novel testing device are r...
in which ρ = density, h = height, ω = angular velocity and r = radius.
Figure 3 shows the respective physical force and its dependence on a bigger radius and higher rotational speed. The results of this study indicate that the centrifugal force represents only a little proportion of effective forces. Hence, the centrifugal forces’ impacts on the tested cells are considered to be insignifican...
Our analysis was focused on two main aspects:
Simulation of the fluid flow characteristics as well as quantification of the arising shear forces at the plate/plate flow chamber with reliable reproducibility
Assessment of the impact of fluid shear stress on osteoblast cells in terms of altered cell morphology and intracellular structural changes
The computational fluid dynamic analysis and the q...
For constant and fully developed laminar flow between the two parallel plates, the magnitude of the wall shear stress (τ) in between was calculated by formula 1:
in which η is the dynamic fluid viscosity (dyn/cm2), r is the radius of the plate (cm), ω stands for angular velocity and H for height (vertical distance in between the two plates).
To get information whether the flow is laminar or t...
A three-dimensional illustration and photography of the plate/plate flow chamber model is shown in Fig. 1. A detailed list of used parts can be found in Appendix 1.
The circulation within the flow chamber was generated by an externally attached electric motor, which rotates up to 500 rounds per minute (rpm). A commercial grade 4 pure medical titanium gear shaft (length = 40 mm, diameter =...
Therefore, the aim of the present study was to establish a new cell chamber model for FSS simulation and stimulation. In addition to its ease of use, the reported model in this study should meet the requirements of a simple design, generating reproducible flow characteristics next to laminar flows and clearly defined flow gradients on implant surfaces.
Cells can be influenced by different mechanostimuli, which lead to an activation of cellular and inter-cellular responses. These reactions may be caused by either a direct stimulation of the cell body (mechanoreception) or indirect cellular stimulation (response) [1,2,3]. Extracellular fluid movement induces fluid shear stress (FSS) that can result in different cellular processes including prolife...
Mechanostimuli of different cells can affect a wide array of cellular and inter-cellular biological processes responsible for dental implant healing. The purpose of this in vitro study was to establish a new test model to create a reproducible flow-induced fluid shear stress (FSS) of osteoblast cells on implant surfaces.
As FSS effects on osteoblasts are detectable at 10 dyn/cm2, a custom-made f...
Fig. 6. Roughness (Sa) box plot
Fig. 6. Roughness (Sa) box plot
Fig. 5. 3D profile
Fig. 5. 3D profile
Fig. 4. CLSM
Fig. 4. CLSM
Fig. 3. SEM for localization of EDX analysis
Fig. 3. SEM for localization of EDX analysis
Fig. 2. SEM. White arrow (→) exemplary mark the droplet like shape of surface as described in the text
Fig. 2. SEM. White arrow (→) exemplary mark the droplet like shape of surface as described in the text
Fig. 1. Diagram of different implant areas used for sampling. 1) Machined (untreated) area. 2) rough (treated) area
Fig. 1. Diagram of different implant areas used for sampling. 1) Machined (untreated) area. 2) rough (treated) area
Amplitude parameters
Group
Name
Sa (μm)
Machined area
WhiteSKY
...
Element composition/semi-quantitative evaluation
Location
Type
Zr at %min–at %max
Hf at %
Y at %min–at %max...
NoneTable 1 Five commercially available ceramic implants and surface characteristics
Beger, B., Goetz, H., Morlock, M. et al. In vitro surface characteristics and impurity analysis of five different commercially available dental zirconia implants.
Int J Implant Dent 4, 13 (2018). https://doi.org/10.1186/s40729-018-0124-8
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Received: 11 December 2017
Accepted: 08 February 2018
Published: 26 April 2018
DOI: https://doi.org/10.1186/s40729-018...
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were m...
Not applicable.
Not applicable.
Beger B, Goetz H, Morlock M, Schiegnitz E, and Al-Nawas B declare that they have no competing interests.
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Department of Maxillofacial Surgery, University Medical Center of the Johannes Gutenberg-University Mainz, Augustusplatz 2, 55131, Mainz, Germany
B. Beger, M. Morlock, E. Schiegnitz & B. Al-Nawas
Biomaterials in Medicine (BioAPP), University Medical Center of the Johannes Gutenberg-University Mainz, Mainz, Germany
H. Goetz
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Papanagiotou HP, Morgano SM, Giordano RA, Pober R. In vitro evaluation of low-temperature aging effects and finishing procedures on the flexural strength and structural stability of Y-TZP dental ceramics. J Prosthet Dent. 2006;96(3):154–64.
Ewais OH, Al Abbassy F, Ghoneim MM, Aboushelib MN. Novel zirconia surface treatments for enhanced osseointegration: laboratory characterization. Int J Dent....
Ong JL, Carnes DL, Cardenas HL, Cavin R. Surface roughness of titanium on bone morphogenetic protein-2 treated osteoblast cells in vitro. Implant Dent. 1997;6(1):19–24.
Schwartz Z, Kieswetter K, Dean DD, Boyan BD. Underlying mechanisms at the bone-surface interface during regeneration. J Periodontal Res. 1997;32(1 Pt 2):166–71.
Al-Nawas B, Gotz H. Three-dimensional topographic and metrologic...
Jacobi-Gresser E, Huesker K, Schutt S. Genetic and immunological markers predict titanium implant failure: a retrospective study. Int J Oral Maxillofac Surg. 2013;42(4):537–43.
Wenz HJ, Bartsch J, Wolfart S, Kern M. Osseointegration and clinical success of zirconia dental implants: a systematic review. Int J Prosthodont. 2008;21(1):27–36.
Shulte W. The intra-osseous Al2O3 (Frialit) Tuebingen...
Aluminum oxide
Ceramic injection molding
Confocal laser scanning microscopy
Energy-dispersive X-ray spectroscopy
Hot isostatic pressing
Implant
Kilovolt
Millibar
Megapascal
Nanometer
Area roughness parameter
Scanning electron microscopy
Sandblasted, Large-grit, Acid-etched
Yttrium-stabilized tetragonal zirconium polycrystalline
Micrometer
New ceramic implants are showing a variety of surface characteristics due to different manufacturing processes as shown by other groups [2, 28]. The surface structures of the investigated implants are close to titanium implants. If the surface characteristics really have a high influence on osseointegration, ceramic implants cannot yet compare to the long experience with titanium. However, there a...
The semi-quantitative energy-dispersive X-ray spectroscopy (EDX) can be used to further analyze the components of the implant surface. None of the implants showed any impurity or unexpected results. Implants 4 and 5 showed yttrium under the detection limit in the EDX analysis. This could be caused by the lower dosage of yttrium endowment in the stabilization processing in comparison to other impla...
The surface shape (droplet-like surface), which was observed in the SEM samples, can be caused due to the sintering process in which ceramic powder was melted and then formed. Different particle, immersion, and droplet sizes can also change due to possible reasons like usage of various types and dosages of acid for the etching process and change of exposure time to acid effect. A longer exposure t...
Implant surface characteristics are of ongoing scientific interest. Implants made from titanium are still the most common to be used. Titanium implants are made from alpha-beta alloy which consists of 6% aluminum and 4% vanadium (Ti-6Al-4V). These materials have low density, high strength, and resistance to fatigue and corrosion, and their modulus of elasticity is closer to the bone than any other...
Implant 2 (Sa 1.27 μm ± 0.24) and implant 5 (Sa 1.22 μm ± 0.36) show the highest roughness values (Sa) of all tested implants: Straumann’s pure ceramic implant was blasted and etched and shows the overall highest Sa value in the rough area. Implant 3 (vitaclinical) shows correspondingly lower Sa around 1.05 μm (± 0.17) (Table 3). The lowest Sa value could be found in implant ...
SEM micrographs presented in Fig. 2 demonstrate the dissimilarity of the sample surface microstructure. Implant 1 shows an overall smoother surface and a slaty-like surface without evidence of a typical etching process. The surface shows sparse roughness. Implants 2–4 show deep markings from their brand’s specific etching and sandblasting processes. In × 10,000 magnification, immersions ca...
Subsequently, the depth map images are imported in the SPIP™ 4.2.6 (Image Metrology) software for roughness and texture evaluation. According to the ISO 25178-2 reference, all surface roughness parameters implemented in SPIP™ are evaluated and classified as amplitude, hybrid, functional, and spatial parameters. Selected values are shown in Table 3.
Analysis of the element composition of the implant surfaces by means of energy-dispersive X-ray spectroscopy (EDX) was performed with an INCA Energy 350 system (Oxford Instruments, Wiesbaden, Germany) coupled with the SEM Quanta 200 FEG (Fig. 2). Similar to the micro-morphological presentation, each implant was divided into comparable sites of interest. Typical areas were selected and evaluated (...
The following five commercially available dental zirconia implants were used in this study (Table 1). Bredent whiteSKY™ implant (I1) is made from unground Brezirkon™, an yttrium oxide (Y2O3)-stabilized tetragonal polycrystalline zirconium oxide and is sandblasted. Zirconium oxide is endowed with 3 mol% yttrium oxide to gain a rectangle and room temperature stable structure [17]. Straumann® ...
Dental implants have become a well-established treatment method for oral rehabilitation after tooth loss. Pure titanium is still the material of choice when it comes to dental intraosseous implants and has been used for decades. However, titanium implants have esthetic limitations, especially in the front aspect of the maxillary jaw. The recession of the gingiva can lead to visible implant necks. ...
The aim of this study was to assess surface characteristics, element composition, and surface roughness of five different commercially available dental zirconia implants.
Five zirconia implants (Bredent whiteSKY™ (I1), Straumann® PURE Ceramic (I2), ceramic.implant vitaclinical (I3), Zeramex® (I4), Ceralog Monobloc M10 (I5)) were evaluated.
The evaluation was performed by means of scanning el...
Fig. 5. Mean and standard deviation of the biomechanical data at both observation periods (P > 0.05). a Removal torque. b Removal energy. c Connection stiffness
Fig. 5. Mean and standard deviation of the biomechanical data at both observation periods (P > 0.05). a Removal torque. b Removal energy. c Connection stiffness
Fig. 4. Comparison among secant and tangent methods to calculate the connection stiffness values, which reveals the absence of mathematical discrepancy
Fig. 4. Comparison among secant and tangent methods to calculate the connection stiffness values, which reveals the absence of mathematical discrepancy
Fig. 3. Representative curve of the torque test for implants. a Graph of torque versus angular displacement with linear regression curve, and equation, representing the connection stiffness. b Determination procedure of unscrewing implant work up to test’s maximum torque
Fig. 3. Representative curve of the torque test for implants. a Graph of torque versus angular displacement with linear r...
Fig. 2. Adaptation of Shimadzu universal testing machine for performing removal torque test of dental implants. a General view. b Assembly detail of connection between Allen keys socket and the implant placed in the tibia
Fig. 2. Adaptation of Shimadzu universal testing machine for performing removal torque test of dental implants. a General view. b Assembly detail of connection between Allen...
Fig. 1. Two pairs of implants (10 mm × 4 mm, L × Ø) from each of the experimental groups were placed in each tibia with an alternating fashion in terms of medio-distal positioning regarding the group, but with the first group chosen at random. Implants were placed with an inter-implant distance of 1 cm
Fig. 1. Two pairs of implants (10 mm × 4 mm, L × Ø) from each of...
Removal torque
Removal energy
Connection stiffness
Spearman’s rho
Removal torque
Coefficient
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df
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F
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de Jesus, R.N.R., Carrilho, E., Antunes, P.V. et al. Interfacial biomechanical properties of a dual acid-etched versus a chemically modified hydrophilic dual acid-etched implant surface: an experimental study in Beagles.
Int J Implant Dent 4, 28 (2018). https://doi.org/10.1186/s40729-018-0139-1
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Received: 01 February 2018
Accepted: 29 May 2018
Published: 2...
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were m...
The animal experimental protocol was approved by the Bioethics Committee for Animal Experimentation (CEUA, protocol no. 098/10) at the Federal University of Uberlândia.
Rainde Naiara Rezende de Jesus, Eunice Carrilho, Pedro V. Antunes, Amílcar Ramalho, Camilla Christian Gomes Moura, Andreas Stavropoulos, and Darceny Zanetta-Barbosa declare that they have no competing interests.
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RNRJ participated in the study concept and design and performed the animal operations, biomechanical test, and data analysis and interpretation. EC, PVA, and AR contributed to define the test protocol and performed the biomechanical test and data analysis. CCGM and DZ participated in the study concept and desig...
Department of Periodontology, Faculty of Odontology, Malmö University, Carl Gustafs väg 34, 205-06, Malmö, Sweden
Rainde Naiara Rezende de Jesus & Andreas Stavropoulos
IBILI, Faculty of Medicine, University of Coimbra, Av. Bissaya Barreto, Bloco de Celas, 3000-075, Coimbra, Portugal
Rainde Naiara Rezende de Jesus & Eunice Carrilho
CEMUC, Mechanical Engineering Department, University of ...
The assistance of fifth-year dental students of the Federal University of Uberlândia in surgeries, including auscultation, and other practicalities is highly appreciated.
The Brazilian Federal Agency for Support and Evaluation of Graduate Education (CAPES research fellow, Full PhD Program, process no. 0975-14.1) provided funding and Neodent® (Curitiba, PR, Brazil) produced the titanium implants...
Kim S, Lee S, Cho I, Kim S, Kim T. Rotational resistance of surface-treated mini-implants. Angle Orthod. 2009;79(5):899–907. https://doi.org/10.2319/090608-466.1.
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de Jesus RNR, Stavropoulos A, Oliveira MTF, Soares PBF, Moura CCG, Zanetta-Barbosa D. Histomorphometric evaluation of a dual acid-etched vs. a chemically modified hydrophilic dual acid-etched implant surface. An experimental study in dogs. Clin Oral Implants Res. 2017;28(5):551–7. https://doi.org/10.1111/clr.12833.
Frost HM. Skeletal structural adaptations to mechanical usage (SATMU): 1. Redefi...
Boyan BD, Cheng A, Olivares-Navarrete R, Schwartz Z. Implant surface design regulates mesenchymal stem cell differentiation and maturation. Adv Dent Res. 2016;28(1):10–7. https://doi.org/10.1177/0022034515624444.
Mamalis AA, Silvestros SS. Analysis of osteoblastic gene expression in the early human mesenchymal cell response to a chemically modified implant surface: an in vitro study. Clin Oral ...
Wall I, Donos N, Carlqvist K, Jones F, Brett P. Modified titanium surfaces promote accelerated osteogenic differentiation of mesenchymal stromal cells in vitro. Bone. 2009;45(1):17–26. https://doi.org/10.1016/j.bone.2009.03.662.
Mamalis AA, Markopoulou C, Vrotsos I, Koutsilirieris M. Chemical modification of an implant surface increases osteogenesis and simultaneously reduces osteoclastogenesis...
Cochran DL, Jackson JM, Jones AA, Jones JD, Kaiser DA, Taylor TD, et al. A 5-year prospective multicenter clinical trial of non-submerged dental implants with a titanium plasma-sprayed surface in 200 patients. J Periodontol. 2011;82(7):990–9. https://doi.org/10.1902/jop.2011.100464.
Wallkamm B, Ciocco M, Ettlin D, Syfrig B, Abbott W, Listrom R, et al. Three-year outcomes of Straumann Bone Level...
Chemically modified sandblasted, large grit, and acid-etched surfaces
Sandblasted, large grit, and acid-etched surfaces
Neodent, Rua Benjamin Lins, 742, Curitiba, PR 80420–100, Brazil
Shimadzu Corporation, Nishinokyo Kuwabara-cho, Nakagyo-ku, Kyoto 604–8511, Japan
IBM Corporation v.23, 1 New Orchard Road, Armonk, New York 10, 504–1722, USA
No significant differences were observed between the specific hydrophilic (SAE-HD) and hydrophobic (SAE) surfaces evaluated in this study, in terms of biomechanical properties during the early osseointegration period.
In fact, the observed lack of differences between the groups could be attributed to the relatively low number of specimens per group. According to the observed data herein, applying a high power (80%) with the present sample size would had revealed a relatively large difference in removal torque equivalent to 43% between the experimental groups. Regarding removal energy and connection stiffness, t...
On the other hand, lack of significant differences between the two groups in the present experiment could be due to the fact that the effect of hydrophilicity, in terms of accelerating bone healing and osseointegration, was unfolded before the first evaluation time-point of 2 weeks, i.e., during the very early healing period. Consistently, pre-clinical investigations show the potential of chemica...
Improving surface wettability aims to increase the implant surface area achieving most favorable protein adsorption and cellular adhesion and thereby to positively regulate the biological response at the initial osseointegration process. Thus, the superior potential of superhydrophilic surfaces in enhancing osseointegration at early stages of bone formation may also enhance their load-bearing capa...
No remarkable events were observed during the surgical procedures and the subsequent healing period. The relative biomechanical performance of both experimental implant surfaces is illustrated in a representative graph of removal torque versus angular displacement. The removal torque, removal energy, and connection stiffness values are described in terms of mean, standard deviation, and 95% confid...
To assess the biomechanical strength of the bone-implant interface, the following parameters were assessed: (a) maximum removal torque (N cm) (primary outcome measure), obtained during the unscrewing process (primary outcome measure); (b) connection stiffness (N cm/rad), corresponding to the ratio between removal torque and angular displacement (secondary outcome measure); and (c) removal energy...
Six male Beagle dogs (~ 1.5 years old), weighting between 13 and 15 kg, were used in the present study. All animals were acclimatized in the experimental animal care facility of Federal University of Uberlândia for 2 weeks previously to the experimental procedures and randomly pair-housed in standard shelters (1 × 1.5 m kennel) to allow environmental enrichment (i.e., variety of toys, ...
The present preclinical in vivo study is reported according to the Animal Research: Reporting of In Vivo Experiments (ARRIVE) guidelines, in regard with relevant items [33]. The animal experimental protocol was approved by the Bioethics Committee for Animal Experimentation (CEUA, protocol no. 098/10) at the Federal University of Uberlândia and followed the normative guidelines of the National Cou...
Evaluation of biological effects and biomechanical properties of innovative technologies in the field of implant dentistry in preclinical animal models, prior to translational research, complies with standard regulations [33]. Thus, the aim of this preclinical animal study was to evaluate the effect of surface microtopography and chemistry on the biomechanical properties of implants with a sandbla...
The progressive evolution of oral implant surface technology (i.e., micro to nanotopography and chemical composition) [1, 2], implant macrogeometry, surgical procedures [3,4,5], and loading protocols [6,7,8] has resulted in high survival and clinical success rates [9]. Accordingly, chemically active micro and nanostructured implant surfaces, presenting moderate surface roughness (Ra/Sa values betw...
In this study, no significant differences were observed between the specific hydrophilic (SAE-HD) and hydrophobic (SAE) surfaces evaluated, in terms of biomechanical properties during the early osseointegration period.
The high survival clinical success rates of osseointegration are requisites for establishing a long-term biomechanical fixation and load-bearing potential of endosseous oral implants. The objective of this preclinical animal study was to evaluate the effect of surface microtopography and chemistry on the early stages of biomechanical rigidity with a sandblasted, dual acid-etched surface, with or w...
Figure 5. Osteoblasts with an orientation tendency after 24 h of rotation (phallacidin fluorescence staining). On the left side with 200× and on the right side with 400× magnification. The yellow arrows show the orientation of the cells. The red arched arrow within the coloured circle shows the direction of rotation. The dashed white line oriented to the right stands for the r...
Figure 4. Randomly orientated osteoblasts without influence of rotation (phallacidin fluorescence staining). On the left side with 200× and on the right side with 400× magnification. The white X on the coloured circle marks the location upon the plate where the osteoblasts were located. The red X marks the centre of the plate
Figure 3. Diagram for visualisation of the calculation of shear stress rates taking into account the centrifugal force and the glass plates’ dimensions. For example, at a distance of 25 mm from the centre of the upper plate, the shear forces’ value is 8.33 dyn/cm2, together with an additional centrifugal force that has a value of 0.55 dyn/cm2
Figure 2. Side view of a computerized simulation, showing the flow chambers’ lower compartment and the flow profile in between the two plates; shearing gap and bottom plate are shown on the left side; rotation speed = 200 rpm; colour code bar (left edge) showing shear force values [Pa] [1 Pa = 10 dyn/cm2]; flow direction presented by arrows
Figure 1. Three-dimensional illustration (a–e) and photography (f) of the experimental setup with the components marked numerical. a 1 Lower petri dish (s’ bottom serving as the lower plate); 2 Rotating glass panel [60 mm diameter (cell bearing)]; 3 Titanium axis. b 4 Liquid medium (red). c 5 Reversed upper petri dish. d 6 Gearwheel with set screw. e 7 Closing; 8 Electronic motor device and ...
References
Ehrlich PJ, Lanyon LE. Mechanical strain and bone cell function: a review. Osteoporos Int. 2002;13(9):688–700.
Vaughan TJ, Haugh MG, Mcnamara LM. A fluid-structure interaction model to characterize bone cell stimulation in parallel-plate flow chamber systems. J R Soc Interface. 2013;10(81):20120900.
Weinbaum S, Cowin SC, Zeng Y. A model for the excitation of osteocytes by mec...
Besides, in the model reported in this study, microscopic examinations are possible after completing the experiment only. Nevertheless, an advantage of the new flow chamber is the possibility of testing different cell colonies simultaneously in one single experiment by placing cells in different radial locations on the spinning disc. Due to the current flow gradient from the centre to the pe...
Due to the fact that constant flows were generated within the parallel flow chamber only, the situations of in vitro experiments differ from in vivo setting where dynamic flow profiles are particular. As the constant laminar flow profile is not physiological in bones, vessels and other tissues, the informative value of the experimental setting is limited but it could be used for various cell...
Further on, the simulations indicated that the flow profile in between the two plates was not influenced by peripheral turbulences alongside the peripheral regions. To verify a cellular realignment towards the shear direction, cells were microscopically examined prior and after exposure to shear forces for 24 h upon a spinning disc at a speed level of 200 rpm. Even if not sufficiently ...
Discussion
The aim of this study was to establish a new FSS model that is easy to use as well as simple to assemble in order to create reproducible fluid shear forces on cells close to implant material surfaces. Todays’ commonly used commercial flow devices differ in geometry and function, which makes comparisons between experiments difficult. The benefits of this novel testing device are...
Regarding the upper compartment, peripheral turbulent flow along the outer edges was similar to the fluid movements within the area in between the plates. At the top, the turbulent flow directed from the centre to the periphery whereas the turbulences at the bottom were orientated in reverse to that. Moreover, the effect of the shear forces on the osteoblast cells was also influenced by the centri...
Results
Our analysis was focused on two main aspects:
Simulation of the fluid flow characteristics as well as quantification of the arising shear forces at the plate/plate flow chamber with reliable reproducibility
Assessment of the impact of fluid shear stress on osteoblast cells in terms of altered cell morphology and intracellular structural changes
Evaluation of the f...
Test procedure
The experimental process involved three steps. First, a count of n = 50.000 commercially available osteoblasts (PromoCell, Heidelberg, Germany) per millilitre of culture medium were cultured on the bottom of the cell-bearing surface (glass panel). Therefore, cells were seeded in a culture medium (cf. Appendix 2 for a detailed composition) at 37 °C. Prior to the test proce...
Analytical formula for evaluating the flow characteristics
Frequently used flow chambers are characterised by an internal fluid flow along a stationary cell-bearing surface, whereas the osteoblast test cells of this newly developed model are circulating within a resting culture medium.
For constant and fully developed laminar flow between the two parallel plates, the magnitude of the wall sh...
Methods
Experimental setup
A three-dimensional illustration and photography of the plate/plate flow chamber model is shown in Fig. 1. A detailed list of used parts can be found in Appendix 1.
The circulation within the flow chamber was generated by an externally attached electric motor, which rotates up to 500 rounds per minute (rpm). A commercial grade 4 pure medical titanium gear shaft (len...
Abstract
Background
Mechanostimuli of different cells can affect a wide array of cellular and inter-cellular biological processes responsible for dental implant healing. The purpose of this in vitro study was to establish a new test model to create a reproducible flow-induced fluid shear stress (FSS) of osteoblast cells on implant surfaces.
Methods
As FSS effects on osteoblasts are detectabl...
Interaksi biokimia langsung antara permukaan implan titanium dan molekul jaringan berjarak pendek. Tipe ikatan kimia yang paling dominan adalah daya van der Waals dan ikatan hidrogen yang lemah, seperti polarisasi dan dipol listrik molekul.Energi permukaan berbanding lurus dengan kecenderungan untuk mengadorpsi molekul. Aturan umumnya adalah bahwa materi dengan ketegangan permukaan anta...
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