Home About us Editorial board Ahead of print Current issue Search Archives Submit article Instructions Subscribe Contacts Login 
  • Users Online: 28
  • Home
  • Print this page
  • Email this page

 Table of Contents  
Year : 2020  |  Volume : 17  |  Issue : 6  |  Page : 439-446

Evaluation of reverse torque values and failure loads of three different abutment designs with internal connections

Department of Prosthodontics, School of Dentistry, Tehran University of Medical Sciences, Tehran, Iran

Date of Web Publication10-Dec-2020

Correspondence Address:
Dr. Azam Sadat Mostafavi
Department of Prosthodontics, School of Dentistry, Tehran University of Medical Sciences, North Kargar Ave, Tehran
Login to access the Email id

Source of Support: None, Conflict of Interest: None

DOI: 10.4103/1735-3327.302891

Rights and Permissions

Background: High percentage of biomechanical complications such as screw loosening in dental implants can be related to implant–abutment (I/A) connection properties which affect the behavior of implant assembly against functional loads in the oral cavity. The aims of the present study were to compare the reverse torque values (RTVs) and failure loads of three abutment types with internal Morse taper connection.
Materials and Methods: In this experimental in vitro study, eighteen implants (4.5 mm × 10 mm bone level implants, Implantium, Dentium Co, Seoul, South Korea) were divided into three groups with different abutments: two-piece (TP) abutment, one-piece (OP) abutment, and screw abutment (SA), mounted in stainless-steel blocks according to ISO 14801. After completion the torque/detorque protocol, a compressive load (1 mm/min) was applied at 30° off-axis until failure. Mean reverse torque/tightening torque (RT/TT) values and failure loads were analyzed with one-way ANOVA test and Tukey's honest significant difference (α = 0.05). Failure modes were evaluated by radiography and stereomicroscopy.
Results: RT/TT values in the TP group were lower than those in other groups (P < 0.001). Highest failure loads were observed in SA group (P = 0.002). In radiographic evaluation, all specimens showed deformation in I/A interface.
Conclusion: I/A connections with larger surface areas may lead to higher RTVs (e.g., OP and SA groups). Use of an additional screw and indexed area in TP group did not reduce the bending resistance under static loading.

Keywords: Compressive loading, dental implant–abutment interface, reverse torque

How to cite this article:
Nokar S, Hajimiragha H, Sadighpour L, Mostafavi AS. Evaluation of reverse torque values and failure loads of three different abutment designs with internal connections. Dent Res J 2020;17:439-46

How to cite this URL:
Nokar S, Hajimiragha H, Sadighpour L, Mostafavi AS. Evaluation of reverse torque values and failure loads of three different abutment designs with internal connections. Dent Res J [serial online] 2020 [cited 2021 Jan 16];17:439-46. Available from: https://www.drjjournal.net/text.asp?2020/17/6/439/302891

  Introduction Top

Although numerous clinical studies have reported high success rates for dental implants, biomechanical complications still occur.[1] Screw loosening – the most common complication is often related to overload and implant–abutment (I/A) connection design.[2] Several reasons are involved in screw loosening like bending moments, connection design, material properties, friction between surfaces, torque sequence, and settling.[3],[4],[5],[6] Screw loosening may cause mechanical complications, such as prosthetic and/or abutment screw fracture, necessitating repair or replacement, which could be exhausting for patients and clinicians.[1] Certain factors, such as connection geometry and abutment insertion torque, contribute to I/A connection stability, especially in single tooth restorations.[7] Sufficient insertion torque is essential for maximum preload to produce clamping force in the screw joint and to reduce the incidence of failures in the I/A interface.[8] To maintain connection stability, the unclamping forces induced by functional loading should not exceed the preload clamping force.[9] It is revealed that high bending moments will result in screw joint instability.[4] Studies have shown that internal conical I/A connection increases joint resistance to unclamping forces, therefore protects the abutment screw.[1],[10],[11],[12],[13] In internal connection system, abutment could be solid (threads are integrated in abutment) or have a separated screw (to permit abutment positional index).[10],[14] Furthermore, they can be selected for cement-retained or screw-retained prosthesis. The preference of these abutments is based on the clinical scenario; however studying the screw joint mechanics and the effects of applied load in I/A interface are valuable for the clinical practice. There exist limited studies to compare the mechanical behavior of one-piece (OP), two-piece (TP) and intermediate abutments' connections in the same system and also varied results. The objectives of this study were to compare reverse torque values (RTVs) and failure loads of three abutment types with internal Morse taper connection. The null hypothesis was that neither RTVs nor failure loads were different among test groups.

  Materials and Methods Top

In this experimental in vitro study, eighteen implant fixtures (Grade 4 titanium, 4.5 mm × 10 mm bone level implants, Implantium, Dentium Co, Seoul, South Korea) were divided into three groups based on abutment type: TP abutment, OP abutment, and screw abutment (SA) [Figure 1] and [Table 1]. Fixture abutments were mounted in a stainless-steel block according to ISO 14801.[15] Fixtures were tapped into a prepared space within the blocks [Figure 2], which were restrained in a metallic holding device. Abutments were tightened according to the company's recommendation torque by using a digital torque meter (Model BGI, Mark-10 Co, Temecula, USA). After 15 min, a second torque was applied to compensate for the settling effect.[16] RTVs were recorded for all samples after 15 min using the same torque meter. In the SA group, copings were made to examine the effect of torquing/detorquing of the prosthetic screw on the abutment screw. Copings were made by using burn-out cylinders that were reinforced with wax (Smooth casting wax, Bego Co, Fort Lauderdale, USA) at the same height as those of the other two groups. Cylinders were cast in base metal alloy (Pors-on 4, DeguDent GmbH, Hanau, Germany) and polished [Figure 3]. Abutment screws in the SA group were tightened and retourqued after 15 min. Prosthetic screws were tightened with 10 Ncm torque according to the company's recommendation, which was repeated after 15 min. RTVs were recorded for prosthetic and abutment screws. To prevent abutment deformation and to ensure accurate load transmission to I/A interface, a cast coping (Wirobond, Bego GmbH, Bremen, Germany) was used during compressive load testing on the TP and OP groups. Compressive load was applied to the specimens at 30° off-axis with a crosshead speed of 1 mm/min in a universal testing machine (UTM, Zwick Z050, ZwickRoell Co, GA, USA) [Figure 4] until failure was evident in the force/displacement curve [Figure 5]. Deviation from linearity in the force/displacement curve indicates plastic deformation; therefore, the point of failure was defined as 0.1 mm of permanent displacement. Failure load data were analyzed by the one-way ANOVA test (α = 0.05). Homogeneity of variances was verified by Levene's test. Mean reverse torque/tightening torque (RT/TT) values among groups and failure loads were analyzed with one-way ANOVA using SPSS software (version 22, IBM Co, New York, USA) and the Tukey's honest significant difference test (α = 0.05).
Figure 1: Studied groups from left to right: two piece, one piece, screw abutment.

Click here to view
Table 1: The properties of the applied materials in the study

Click here to view
Figure 2: Stainless steel block designed to mount the specimens.

Click here to view
Figure 3: Burn-out cylinder's wax up and casting in screw abutment group.

Click here to view
Figure 4: Samples were loaded 30° off axes in the universal testing machine.

Click here to view
Figure 5: Force/displacement curve and point of failure was recorded for each specimen.

Click here to view

Radiographic investigation of abutment deflection was performed by repositioning I/A assembly in a silicone index [Figure 6]. Radiographs were taken with the beam perpendicular to I/A connection at 5 mm distance (RVG, Carestream Dental LLC). Digital images were saved and the amount of deflection was observed through superimposition of the images before and after loading in the Photoshop program (version 10, Adobe Inc., California, USA) [Figure 7]. Additionally, I/A interfaces were evaluated by stereomicroscope with a magnification of ×50 (SZX12, Olympus Optical Co., LTD, Tokyo, Japan) [Figure 8] and macroscopically through unscrewing the abutments (the abutments could be retrieved in 50% of all specimens by using torque meter). A brand new abutment was torqued in the fixtures in those specimens that abutments could be retrieved. The new I/A connection was investigated for deformation in the implant crest module by using the stereomicroscope following the previous protocol. The methodology of the present study was reviewed and verified by an independent statistician.
Figure 6: Making silicone indexes (left) for holding implant–abutment assemblies during radiation (right).

Click here to view
Figure 7: Image superimposition to analyze the amount of deflection.

Click here to view
Figure 8: Stereomicroscope view from implant–abutment connection after loading.

Click here to view

  Results Top

One-way ANOVA revealed significant difference between tested groups (P < 0.05). Thus, there was a statistically significant difference in RT/TT values of experimental groups which is presented in [Table 2]. All specimens in the TP group showed RT/TT values <1.0. Conversely, all but one of the RT/TT values in the OP group were >1.0. In the SA group, 50% of RT/TT values were >1.0. Furthermore, RT/TT values for all prosthetic screws were <1.0. In SA group, when prosthetic screws were detorqued, the RT/TT values of abutment screws became <1.0 in all specimens. Based on the post hoc test, the RT/TT values in the TP group were statistically lower than those in the OP and SA groups (P < 0.001), whereas the values in the OP and SA groups were similar [Table 3].
Table 2: One.way ANOVA results of reverse torque/tightening torque (%) differences among the groups (P<0.05)

Click here to view
Table 3: Results of reverse torque/tightening torque and mean failure loads (n) in studied specimens

Click here to view

In compressive loading test, ANOVA results indicated significant differences among the groups [Table 4]. According to post hoc test, TP and OP groups showed lower failure loads than SA group (P = 0.002) without a significant difference between them [Table 3].
Table 4: One-way ANOVA results of mean failure load differences among the groups (P<0.05)

Click here to view

In radiographic evaluation, deflection was detected in the conical part of all abutments [Figure 7]. In stereomicroscopic studies, a gap was observed on the same side of the abutment loading between the abutment and fixture platform [Figure 8] and [Figure 9]. After loading, unlike the SA group, no abutments in the TP group could be retrieved, and only three abutments were unscrewed in the OP group. In retrieved abutments, deformation was found in the conical part of the abutments.
Figure 9: The border between conical part and gingival height of abutment after loading test was not level with the fixture platform because of deformation.

Click here to view

  Discussion Top

Based on the findings of this study, the RT/TT values and failure loads showed significant differences among the three test groups. Therefore, the null hypothesis was rejected.

Stability of the screw joint is primarily provided by the insertion torque which develops “preload.” Preload is influenced by the magnitude of the torque, the design of the screw head, the number and design of the threads, the composition of the metal, the fit of the components, the surface conditions, and the screw diameter.[17] The design of the screw head should allow maximum torque to be transferred along the screw stem.[18] A flat-head screw is common in implant systems and is believed to generate a more favorable stress pattern.[19] In contrast to the conical-head design, the flat-head screw has less tendency to deform the nonpassive casting, which may blind its misfit.[20] In the current study, the screw head design in the prosthetic screw and TP group was flat. However, in OP and SA groups, the screw was integrated with the conical part of the abutment. Therefore, in TP group, the forces were distributed more evenly along the screw, whereas in OP and SA groups, more stress was localized in the upper parts of the screw stem. Except abutment screw design, test groups were similar in terms of other above factors as mentioned in the methods.

Torque/detorque test

The OP group had the highest RT/TT values, followed by SA and TP group. I/A contact surface area in OP and SA groups was 20.09 mm2. In TP group, which had a hexagonal index, the contact surface area was 13.92 mm2 (according to system catalogue information). Less contact surface (31%) in TP group can be a reason for the lower RT/TT values compared to OP and SA groups. Along with this result, Cehreli et al.[14] indicated that the presence of the index area in ITI abutments leads to a lower contact surface area and subsequently, lower RTVs. Also, Ding et al.[21] reported that the initial removal torques of the solid abutment were significantly higher than the synOcta abutment. Recent result confirms the role of friction in preload maintenance. In consistent to the result of present study, Cerutti-Kopplin et al.,[22] de Oliveira Silva et al.[23] and Pintinha et al.[24] revealed higher RTVs in solid conical abutments rather than TP abutments. More I/A conical contact provides more intimate contact which in turn may increase the probability of cold welding and subsequently RTVs,[10] as occurred in most of OP and SA group specimens (mean RTVs was almost 2%–8% higher than tightening torque values (TTVs)). This phenomenon has been confirmed in solid conical abutments in some studies.[25],[26],[27] Sutter et al.,[25] argued that the precise machining of the mated parts with <10 μm spacing further heightens the security of this interface design. However torque loss has been reported for this kind of abutment in some studies.[4],[22],[23],[24] RTVs of TP group in the present study revealed 30% reduction which was similar to Cehreli et al.'s[14] study (36% reduction). Furthermore, Tsuge and Hagiwara[28] reported a 20% reduction in the RTV of an internal connection TP abutment. In addition, other studies have addressed 15%, 11% and 40% torque loss in indexed TP abutments.[22],[23],[24] Beside less I/A contact surface, it seems that internal indexed feature of the TP group may provide more freedom of movement due to manufacturing tolerance, which may have effect on RTVs. Different results in studies can be attributed to different value and modality of initial torque, connection design, and components tolerance. In the SA group, the detorque value of the abutment screw decreased after detorquing the prosthetic screw. This result may imply that in a similar clinical scenario with prosthetic screw loosening and/or replacement, the abutment screw should be retorqued. Nevertheless, this finding is based on an in vitro study and further investigation is recommended.

Loading test

Failure loads in the experimental groups fell within the range of 750–2300 N, which is higher than the common chewing force in the anterior and posterior regions (109 and 250 N, respectively).[29] Hence, all test groups displayed sufficient strength to withstand occlusal forces, which is in agreement with studies by Cehreli et al.[14] and Ding et al.[21] However, the applied force in this study was static; multivectoral forces and fatigue processes in the oral condition may modify the result. The mean failure forces in the OP and TP groups were comparable (820.8 vs. 865 N). Cehreli et al.[14] indicated that unlike OP abutments with friction between conical parts, TP abutments are retained mostly by the torque applied on the abutment screw. Nevertheless, it seems that the precise mating of the indexed region in the TP abutment with its counterpart in the implant provides sufficient resistance to torsion and dynamic loads.[14] In Ding et al.'s study,[21] failure loads at the beginning of plastic deformation of the OP and TP abutments were 1407.6 and 1256.8 N, which are higher than values of similar groups in the present study. Balfour and O'Brien[30] demonstrated that failure loads were 814 N in a group with a hexagonal internal connection and 587 N in a group with an octagonal internal connection, although a clear definition of failure was not provided. In a study by Möllersten et al.,[31] mean failure loads at the beginning of plastic deformation of seven implant systems were in the range of 137–693 N. The authors related this finding to the connection depth. In this regard, Steinebrunner et al.[32] applied a load-to-fracture protocol and reported greater fracture strength with longer connections (replace 1542 N and Camlog 1467 N). Park et al.[33] also reported similar result in their research. In the present study, the connection depth in the TP group was less than that of the OP or SA group. However, failure loads of the TP and OP groups were comparable, which could be explained by the load resistance of the internal hexagon. Consistent to the present result, Zancopé et al.[34] concluded that the presence of a prosthetic index on Morse taper abutments did not influence the fracture resistance. Moreover, a separate screw in the TP abutment of Astra Tech had no influence on flexural forces in the I/A conical connection compared to the OP abutment, as demonstrated by Norton.[4] Different failure loads can be linked to different system designs, initial torque and different failure definition in studies. The mean failure load in SA group was significantly higher than OP group which can be attributed to differences in their design and mechanics. The OP abutment in the OP group has more height than the SA in the SA group, which results in a larger lever arm that could make them more susceptible to bending. In the OP group, the loads are distributed in a single screw joint, whereas two joints exist in the SA group. May be that is because of two screw joints (SA group) offers a more favorable stress distribution; this possibility should be investigated in further studies. In line with the findings of the present study, Erneklint et al.[35] reported different mean failure loads for 20° and 45° uniabutments in the Astra system (1280–157 N, 450–530 N). The only difference between specimens was the amount of taper in the upper part of the components. These findings indicate that the abutment design plays an effective role in load bearing.

Radiographic and macroscopic evaluation

Different failure modes have been reported in the literature, including failure in the first thread of the abutment screw,[30] bending/breaking of the abutment screw,[36],[37] bending in the concave area above the threads,[4] and bending in the abutment base.[21] In the present study, after loading, deformation of the TP abutment (TP group) was less than that of the OP abutments (OP and SA groups), as evidenced by X-ray superimposition [Figure 7]. In other words, deformation in TP abutments occurred in the cervical part of the abutment base and in the threadless part of the abutment screw, which justifies the lack of irretrievability of these abutments after loading.

After retrieving the abutments and fastening a brand new abutment, a gap was observed in I/A connection area; this may indicate distortion in the narrower cervical part of the fixture. Consistent with the result of the present study, Ding et al.,[21] Balfour and O'Brien,[30] and Strub and Gerds[36] found deformation in the cervical part of the implants. The relationship between the microgap and loading deformation in the I/A connection deserves further studies. Magnified digital radiographic images revealed that the first thread of the abutment screw was compressed on the bending side and stretched on the opposite side. The upper portion of the abutment screw shaft was not supported by its counterpart in the implant body, which could explain the deformation of this part in the TP group. It seems that the conical part of the abutment endures more force and protects the threads against overload.[14] In the SA group, the fit between coping and abutment after loading remained intact, and the prosthetic screws did not show any deformation. In retrieved abutments (OP and SA groups), deformation was evident in the abutment base. It seems that the different failure modes in various systems were due to different designs, such as the degree of taper, connection of the threads with the conical part, and the material used. Irretrievability of the abutment or deformation of the implant crest module can have serious consequences that can complicate reconstruction of the assembly.

As an in vitro study, the results of this research cannot be extrapolated to the clinical situation. However, in vitro studies can provide useful information about the comparison of failure resistance between implant systems. Moreover, the results can be used to design future studies with similar conditions in the oral environment.

  Conclusion Top

Within the limitations of this in vitro study, it can be concluded that greater surface area in the I/A connection leads to more adaptation between adjacent surfaces and increased RTV. Separate screw and indexed area in TP abutments did not reduce the bending resistance under static loading in the I/A interface compared to OP abutments. It is recommended that SAs be retorqued in the case of prosthetic screw loosening.

Financial support and sponsorship


Conflicts of interest

The authors of this manuscript declare that they have no conflicts of interest, real or perceived, financial or nonfinancial, in this article.

  References Top

Merz BR, Hunenbart S, Belser UC. Mechanics of the implant-abutment connection: An 8-degree taper compared to a butt joint connection. Int J Oral Maxillofac Implants 2000;15:519-26.  Back to cited text no. 1
Goodacre CJ, Kan JY, Rungcharassaeng K. Clinical complications of osseointegrated implants. J Prosthet Dent 1999;81:537-52.  Back to cited text no. 2
Meng JC, Everts JE, Qian F, Gratton DG. Influence of connection geometry on dynamic micromotion at the implant-abutment interface. Int J Prosthodont 2007;20:623-5.  Back to cited text no. 3
Norton MR.In vitro evaluation of the strength of the conical implant-to-abutment joint in two commercially available implant systems. J Prosthet Dent 2000;83:567-71.  Back to cited text no. 4
Nithyapriya S, Ramesh AS, Kirubakaran A, Mani J, Raghunathan J. Systematic analysis of factors that cause loss of preload in dental implants. J Indian Prosthodont Soc 2018;18:189-95.  Back to cited text no. 5
[PUBMED]  [Full text]  
Lee JH, Cha HS. Screw loosening and changes in removal torque relative to abutment screw length in a dental implant with external abutment connection after oblique cyclic loading. J Adv Prosthodont 2018;10:415-21.  Back to cited text no. 6
Theoharidou A, Petridis HP, Tzannas K, Garefis P. Abutment screw loosening in single-implant restorations: A systematic review. Int J Oral Maxillofac Implants 2008;23:681-90.  Back to cited text no. 7
Balshi TJ, Hernandez RE, Pryszlak MC, Rangert B. A comparative study of one implant versus two replacing a single molar. Int J Oral Maxillofac Implants 1996;11:372-8.  Back to cited text no. 8
Pedroza JE, Torrealba Y, Elias A, Psoter W. Comparison of the compressive strength of 3 different implant design systems. J Oral Implantol 2007;33:1-7.  Back to cited text no. 9
Norton MR. Assessment of cold welding properties of the internal conical interface of two commercially available implant systems. J Prosthet Dent 1999;81:159-66.  Back to cited text no. 10
Schwarz MS. Mechanical complications of dental implants. Clin Oral Implants Res 2000;11 Suppl 1:156-8.  Back to cited text no. 11
Park JK, Choi JU, Jeon YC, Choi KS, Jeong CM. Effects of abutment screw coating on implant preload. J Prosthodont 2010;19:458-64.  Back to cited text no. 12
Schmitt CM, Nogueira-Filho G, Tenenbaum HC, Lai JY, Brito C, Döring H, et al. Performance of conical abutment (Morse taper) connection implants: A systematic review. J Biomed Mater Res A 2014;102:552-74.  Back to cited text no. 13
Cehreli MC, Akça K, Iplikçioǧlu H, Sahin S. Dynamic fatigue resistance of implant-abutment junction in an internally notched Morse-taper oral implant: Influence of abutment design. Clin Oral Implants Res 2004;15:459-65.  Back to cited text no. 14
IOf S. International Standard ISO 14801-Dentistry-Implants -Dynamic Fatigue test for Endosseous Dental Implants. Geneva: International Organization for Standardization; 2007.  Back to cited text no. 15
Kim KS, Lim YJ, Kim MJ, Kwon HB, Yang JH, Lee JB, et al. Variation in the total lengths of abutment/implant assemblies generated with a function of applied tightening torque in external and internal implant-abutment connection. Clin Oral Implants Res 2011;22:834-9.  Back to cited text no. 16
Misch CE. Dental Implant Prosthetics. 2nd ed. St Louis: Mosby/Elsevier; 2015. p. 726-9.  Back to cited text no. 17
Jörnéus L, Jemt T, Carlsson L. Loads and designs of screw joints for single crowns supported by osseointegrated implants. Int J Oral Maxillofac Implants 1992;7:353-9.  Back to cited text no. 18
Binon P. The role of screws in implant systems. Int J Oral Maxillofac Implants 1994;9 suppl: 48-63.  Back to cited text no. 19
Gupta S, Gupta H, Tandan A. Technical complications of implant-causes and management: A comprehensive review. Natl J Maxillofac Surg 2015;6:3-8.  Back to cited text no. 20
[PUBMED]  [Full text]  
Ding TA, Woody RD, Higginbottom FL, Miller BH. Evaluation of the ITI morse taper implant/abutment design with an internal modification. Int J Oral Maxillofac Implants 2003;18:865-72.  Back to cited text no. 21
Cerutti-Kopplin D, Rodrigues Neto DJ, Lins do Valle A, Pereira JR. Influence of reverse torque values in abutments with or without internal hexagon indexes. J Prosthet Dent 2014;112:824-7.  Back to cited text no. 22
de Oliveira Silva TS, Mendes Alencar SM, da Silva Valente V, de Moura CDVS. Effect of internal hexagonal index on removal torque and tensile removal force of different Morse taper connection abutments. J Prosthet Dent 2017;117:621-7.  Back to cited text no. 23
Pintinha M, Camarini ET, Sábio S, Pereira JR. Effect of mechanical loading on the removal torque of different types of tapered connection abutments for dental implants. J Prosthet Dent 2013;110:383-8.  Back to cited text no. 24
Sutter F, Weber HP, Sorenson J, Belser U. The new restorative concept of the ITI dental implant system: Design and engineering. Int J Periodont Rest Dent 1993;5:409-32.  Back to cited text no. 25
Squier RS, Psoter WJ, Taylor TD. Removal torques of conical, tapered implant abutments: The effects of anodization and reduction of surface area. Int J Oral Maxillofac Implants 2002;17:24-7.  Back to cited text no. 26
Feitosa PCP, de Lima APB, Silva-Concílio LR, Brandt WC, Claro Neves AC. Stability of external and internal implant connections after a fatigue test. Eur J Dent 2013;7:267-71.  Back to cited text no. 27
  [Full text]  
Tsuge T, Hagiwara Y. Influence of lateral-oblique cyclic loading on abutment screw loosening of internal and external hexagon implants. Dent Mater J 2009;28:373-81.  Back to cited text no. 28
Craig RG. Restorative Dental Materials. 6th ed. St Louis: Mosby; 1980, p. 60-1.  Back to cited text no. 29
Balfour A, O'Brien GR. Comparative study of antirotational single tooth abutments. J Prosthet Dent 1995;73:36-43.  Back to cited text no. 30
Möllersten L, Lockowandt P, Lindén LA. Comparison of strength and failure mode of seven implant systems: An in vitro test. J Prosthet Dent 1997;78:582-91.  Back to cited text no. 31
Steinebrunner L, Wolfart S, Ludwig K, Kern M. Implant-abutment interface design affects fatigue and fracture strength of implants. Clin Oral Implants Res 2008;19:1276-84.  Back to cited text no. 32
Park SJ, Lee SW, Leesungbok R, Ahn SJ. Influence of the connection design and titanium grades of the implant complex on resistance under static loading. J Adv Prosthodont 2016;8:388-95.  Back to cited text no. 33
Zancopé K, Resende CC, Tavares LN, Neves FD. Influence of indexed abutments on the fracture resistance of internal conical dental implants. Gen Dent 2017;65:e14-e16.  Back to cited text no. 34
Erneklint C, Odman P, Ortengren U, Karlsson S. An in vitro load evaluation of a conical implant system with 2 abutment designs and 3 different retaining-screw alloys. Int J Oral Maxillofac Implants 2006;21:733-7.  Back to cited text no. 35
Strub JR, Gerds T. Fracture strength and failure mode of five different single-tooth implant-abutment combinations. Int J Prosthodont 2003;16:167-71.  Back to cited text no. 36
Boggan RS, Strong JT, Misch CE, Bidez MW. Influence of hex geometry and prosthetic table width on static and fatigue strength of dental implants. J Prosthet Dent 1999;82:436-40.  Back to cited text no. 37


  [Figure 1], [Figure 2], [Figure 3], [Figure 4], [Figure 5], [Figure 6], [Figure 7], [Figure 8], [Figure 9]

  [Table 1], [Table 2], [Table 3], [Table 4]


Similar in PUBMED
   Search Pubmed for
   Search in Google Scholar for
 Related articles
Access Statistics
Email Alert *
Add to My List *
* Registration required (free)  

  In this article
Materials and Me...
Article Figures
Article Tables

 Article Access Statistics
    PDF Downloaded39    
    Comments [Add]    

Recommend this journal