IP Annals of Prosthodontics and Restorative Dentistry

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Online ISSN: 2581-480X

IP Annals of Prosthodontics and Restorative Dentistry (APRD) open access, peer-reviewed quarterly journal publishing since 2015 and is published under the Khyati Education and Research Foundation (KERF), is registered as a non-profit society (under the society registration act, 1860), Government of India with the vision of various accredited vocational courses in healthcare, education, paramedical, yoga, publication, teaching and research activity, with the aim of faster and better dissemination more...


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Prakash and Narayanan: Biomechanics in dental implants


Introduction

Dental biomechanics is defined as the relationship between the biologic behavior of oral structures and the physical influence of a dental restoration [GPT-9].

Biomechanics comprises of all kinds of interactions between tissues of the body and forces acting on them and response of the tissues to the applied loads.1 The loads acting on the dental implant are transferred to the surrounding biological tissues. Implant biomechanics can be reactive or therapeutic in nature. It deals with biomechanical factors that are of destructive nature to the implants and the clinical process of altering each biomechanical factor to reduce the cumulative response causing implant overload.2 The biomechanics acting on a natural tooth and implant differ due to various reasons. (Table 1, Figure 2)

Implant biomechanics can be explained under following heads-

Figure 0
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Figure 1

Differences between natural tooth and implants

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Discussion

Forces acting on the Implant

Forces applied to the implant may be assessed in type, direction, magnitude, duration and presence of any parafunctional forces. From the simple mathematical equation of Stress = Force ÷ Surface area, it can be observed that, to decrease the stress, the functional surface area should increase or the force should decrease.

Cowin in 1989 suggested that cortical bone is strongest in compression and also can be well tolerated by the bone-implant system.3 Shear and tensile forces, being angular in nature, direct stresses over the crestal bone and bone-implant interface, which can be detrimental to implant in the long run. A 30-degree angled load will increase the overall stress by 50% compared to the load applied along the long axis. 4

The magnitude of forces applied varies based on the anatomical region, age, gender and state of dentition. Craig in 1980 described that the magnitude of bite force is greater in the molar region (200 lb), less in the canine area (100 lb), least in the anterior incisor region (25 to 35 lb) and increases upto 1000lb in the presence of parafunctional habits such as bruxism, clenching and tongue thrusting.5 These parafunctional habits increase the duration of bite forces, that exceed the endurance limit of the implant components and can lead to screw loosening or fatigue failure. 6

Implant related factors

Implant design should maximize implant surface area and create a better spreading of stress and primary stability. 7(Figure 3)

Figure 2

Implant design consideration; a)Thread Macrodesign. b) Implant length. c) Implant width. d) Crest Module

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Implant macro design

Thread shape and stress distribution: The thread shapes in dental implants are developed for easier insertion and force transmission to surrounding bone. Using a linear motion through rotation, threaded implants are inserted into the osteotomy site. Thread shapes available for screw-retained implants include square shape, V-shape, buttress and reverse buttress threads, which are defined by the thread thickness and face angle. Implant threads increase surface contact area and favourable forces while reducing adverse stimuli.

Using Finite Element Analysis, Chia Ching Lee and his colleagues evaluated the effects of implant threads (symmetrical, square and buttressed) on the contact area and stress distribution of marginal bone. 8 Among the three thread shapes, the contact area with square thread was highest and the force dissipation around marginal bone was least. In a study by Eraslanet al, performed with four different thread forms under a static axial load of 100 N, it was observed that maximum stress was concentrated at the cervical cortical regions around the first thread and the stress value was lowest in the square thread type. 9

Thread pitch and lead

Pitch is an important geometric factor that determines the bone-to-implant contact (BIC) and the biomechanical load distribution. Thread pitch is defined as the distance between two neighbouring threads, measured on the same side of the axis, It also refers to the number of threads per unit length. implants having smaller pitch indicates more threads, leading to greater surface area.10 In a histological analytical study conducted by Paolo Trisi et al on sheep bone, it was observed that large threaded implants showed significantly higher %BIC and %BV than small threaded implants in low-density bone and statistically higher secondary stability in cancellous and cortical bones. 11

Lead is the distance within the same thread before and after one complete rotation in the axial direction. That is, for single, double, and triple-threaded implants, lead increases by one, two, and three times the pitch respectively. Lead indicates the distance that an implant would move after one turn and it plays an important role on determining the speed of implant insertion. A FEA conducted by Yoko Yamaguchi suggested that, to achieve good primary stability, increasing the thread length and reducing the pitch/lead and lead angle to that of a single-threaded implant is considered more effective versus using a double-threaded implant. 12

Thread depth and width

According to Misch, thread depth is the distance from the outermost tip to the innermost body of the thread.7 He defines thread width as the distance between the superior most and inferior-most tip of a single thread measured axially. Shallow thread depth implants, allow an easy implant placement, especially in the high-density bone. Implants with deep thread depth can be used in low density bone, to increase the functional surface area. A study conducted by Sun-Young Lee et al to evaluate the effect of thread depth on primary stability in low density bone concluded that implant with deep threads provide better mechanical stability in areas of low density bone.8

Various implant systems are available using progressive threads; for example, Ankylos (Dentsply Friadent, Mannheim, Germany). In this thread form, thread depth gradually decreases from the apical end to the coronal neck of the implant. 13

Implant length and width

An increase in implant length has a benefit for initial stability as overall total surface area increases. It provides resistance to torque or shear forces and also achieves bicortical stabilization.

Wider root form implants have a greater area of bone contact and help in dissipation of forces over a wider area.

Each 0.25 mm increase in implant diameter may increase the overall surface area 5% to 10% in a cylinder implant body.

Hamidreiza in his study evaluated the influence of mechanical characteristics of the implant on primary stability in different bone types, based on resonance frequency analysis (RFA). He concluded that in cases with D1 type of bone, implant length did not have significant increase in primary stability. But in cases with low density bone, increasing implant width and length helps achieve primary stability. The greater diameter not only decreases stress but also decreases the likelihood of implant fracture. 14

Crest module considerations

The crest module of an implant body is the transosteal region, the crest module of the implant has a surgical influence, a biological width influence, a loading profile consideration (characterized as a region of highly concentrated mechanical stress).15 The crest module seals completely the osteotomy, providing a barrier and deterrent for the ingress of bacteria or fibrous tissue during initial healing. (Table 2)

Apical design consideration: round cross section implants donot resist torsional shear forces when abutment screws are tightened. Hence, anti-rotational features are added.

Implant Microtopography

Alteration of microtopography of implant is done using sandblasting, acid etching, grit blasting which create imperfection along the machined surface, thusincreasing surface area and attracting osteogenic cells to cause bone formation.

Implant Nano-topography

Comprises of Cell-implant interaction at cellular and protein level. It includes anodic oxidation, laser ablation, TiO2 blasted implants. These implants are proven to prevent crestal bone loss and increase soft tissue seal. 16, 17

Loading protocols

Misch in 1980 proposed that gradual increase in occlusal load separated by a time interval to allow bone to accommodate. 7

Softer bone— increase in progressive loading period.

Protocol includes time, diet, occlusal consideration, prosthesis design. 18

Bone factors: 7, 19 (Fig 3)

Density of bone

Bone constitute the ideal case for implant placement.

Figure 3

Bone Factors

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  1. Available bone height: Measured from crest of ridge to opposing anatomical landmark. Related to density of bone.High density bones- shorter implants can be accommodated.Low density bones- longer implants needed.

  2. Available bone width: Wider ridges allow placement of wider implants, thus increasing surface area and force dissipation.

  3. Available bone length: Length minimum should be 8mm

  4. Bone angulation: Ideally, bone is perpendicular to the plane of occlusion,aligned with the forces of occlusion and is parallel to the long axis of prosthodontic restoration. Bone angulation should be less than 30o. 20

Clinical moment arms

A total of six moments (rotations) may develop about the three clinical coordinate axes previously described:occluso-apical, labiolingual and mesiodistal axes( Such moment loads induce microrotations and stress concentrations at the crest of the alveolar ridge at the implant-tissue interface, which lead to crestal bone loss.

Three clinical moment arms exist in implant dentistry

  1. Occlusal height.

  2. Cantilever length.

  3. Occlusal width.

Minimization of each of these moment arms is necessary to prevent unretained restorations, fracture of components, crestal bone loss, or complete implant system failure.

Occlusal height

Directed along facio-lingual axis-Working or balancing occlusal contacts.

Mesio-distal axis- tongue thrusts or peri-oral musculature.

Vertical axis- no moment load induced.

Cantilever length:21

Vertical axis- large moment arms.

Lingual force component- twisting moment on implant neck axis.

Force directly on implant- no moment loads, torque or rotation induced.

Figure 4

Clinical moment arms

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Figure 5

Antero-posterior distance for cantilever

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Considerations for Cantilevered prosthesis (Figure 6)

Clinical experiences suggest that the distal cantilever should not extend 2.5 times the A-P distance under ideal conditions [to achieve stabilizing effect].

Patients with parafunction not to be restored with cantilever - More offset loads are applied.

Tapered arch forms offer larger AP distance than square arch forms. (Table 3)

Table 1

Differences between natural tooth and implant

Natural tooth

Implant

Has periodontal ligament, shock absorption capacity

‘Functional ankylosis’ to bone

Shows flexion

Is rigid or stiff

Stress is distributed evenly to surrounding bone

Stress concentrates over crestal bone

Proprioception of about 20 µm

Proprioception of 48-64 µm and around 106 µm in case of implant over dentures

Apical intrusion by about 28 µm and lateral movement by around50-108 µm

Apical movement observed is around 10-30 µm

Table 2

Crest module considerations

Larger crest module diameter

Increases surface area

Decrease stress at the crestal region

Increases the platform of the abutment connection

Reduced stress to the abutment screw during lateral loading

Smooth collar

Reduction of plaque accumulation and improved hygiene.

Extended smooth collar

Shear load- crestal bone loss

Table 3

Forces acting on cantilevered prosthesis

Load applied

Forces acting

100 N force on implant

No moment loads, torque or rotation

Load on cantilever at 1 cm distance

100Ncm load

At 2 cm distance

200Ncm load

At 3 cm distance

300Ncm load

Implants tightened with 30Ncm torque

Table 4

Bone mechanics and implant considerations

Bone density

Implant consideration

Rationale

D1, D2 (High/ medium density bone)

Shorter implants

Narrow implants

Shallow thread depth implants

Implant with lesser threads

Ideal crown height space

More intimate contact of bone with implant surface

Lesser moment loads acting on implant

Forces dissipated along long axis of implant

Lesser healing time FP1, FP2 prosthesis

Cantilevered prosthesis can be considered

D3, D4 (Low density bone)

Longer implants

Wider implant

Deep thread implants

Lesser pitch implants

Coated implants

Increased crown height space

To achieve increased functional surface area

More clinical moment arms acting, more rotation and torquing forces

Shear and tensile forces present RP4, RP5 prosthesis

Occlusal width

Wide occlusal table- Facio-lingual tipping (rotation) increased.

Narrow table- provides more centric contacts.

Conclusion

The success of the therapy in Oral implantology is dependant equally on principles of biomechanics and strict clinical protocol adherence. Failures result if either of these are not followed or taken into consideration. Biomechanics are involved in the conception of a new implant prototype (determining the need for certain modifications to existing designs), producing and testing (in vitro and in vivo) of the implant and all the clinical stages (planning, insertion, loading, maintenance).

Although modern day implants are versatile, present high success rates, increased patient acceptance and comfort, the scope still exists for improvement and research and d evelopment should be directed towards it.

Conflict of Interest

The authors declare that there are no conflicts of interest in this paper.

Source of Funding

None.

References

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C E Misch M W Bidez CE Misch A scientific rationale for dental implant designContemporary implant dentistry. 2nd Edn.St Louis, Mosby1999

2 

C E Misch Early crestal bone loss etiology and its effect on treatment planning for implantsD3Dental Learning Systems Co, Inc1995317

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S C Cowin Bone mechanics, Boca Raton, FlaCRC Press1989

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CC Lee SC Lin MJ Kang SW Wu PY Fu Effects of implant threads on the contact area and stress distribution of marginal boneJ Dent Sci20105315665

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O Eraslan O Inan The effect of thread design on stress distribution in a solid screw implant: A 3D finite element analysisClin Oral Investig2010144411610.1007/s00784-009-0305-1

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Yamaguchi Effect of implant design on primary stability using torque time curves in artificial boneInternational Journal of Implant Dentistry2015112110.1186/s40729-015-0024-0

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S Hansson The implant neck: Smooth or provided with retention elements. A biomechanical approachClin Oral Implants Res1999105394405

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S Szmukler-Moncler H Salama Y Reingewirtz J H Dubruille The timing of loading and the effect of micro- motion on the dental implant-bone interface: A review of the experimental literatureJ Biomed Mater Res1998432192203

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C E Misch Density of bone: Effect on treatment plans, surgical approach, healing, and progressive loadingInt J Oral Implant1990622331

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© This is an open access article distributed under the terms of the Creative Commons Attribution-NonCommercial-ShareAlike 4.0 International License which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.


Article type

Review Article


Article page

131-136


Authors Details

Poonam Prakash, Ambika Narayanan


Article History

Received : 07-08-2021

Accepted : 25-08-2021

Available online : 21-09-2021


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