Variation of the ultrasonic response of a dental implant embedded in tricalcium silicate-based cement under cyclic loading
Introduction
The use of bone substitute biomaterials in the context of dental implant surgery has become a common technique used for edentulous patients with poor bone quality. Different biomaterials have been used as bone substitute material such as autogenous (Khoury et al., 2007, Rickert et al., 2012), allogeneic (Waasdorp and Reynolds, 2010) and xenogeneic (Simion and Fontana, 2004, Taschieri et al., 2010) bone grafts as well as different synthetic biomaterials (Davies et al., 2010).
Autogeneous bone graft has good clinical performances but constitutes a relatively invasive surgical procedure. Allogeneic bone graft can be considered as a good alternative because of the greater amount of material available and the possibility of using local anesthesia only. However, allograft requires a longer period for bone regeneration and the risk of rejection and infection may be higher (Jones, 2008). Therefore, xenogeneic bone graft has been employed using biomaterials such as coral or animal bone tissue, which are easier to handle (Simion and Fontana, 2004, Eppley and Dadvand, 2006). Another option lies in using synthetic biomaterials which may be easier to produce (Shigeishi et al., 2012) and injectable (Gauthier et al., 1999). Different biomaterials of synthetic origin have been developed such as calcium phosphate ceramic (Morimoto et al., 2012) and bioglass (Kenny and Buggy, 2003, Trindade-Suedam et al., 2010). Among the different calcium phosphate ceramics, β-tricalcium phosphate (Podaropoulos et al., 2009), hydroxyapatite material (Kenny and Buggy, 2003, Shigeishi et al., 2012) and a mix of both (Yamada et al., 1997) have been used as bone substitute materials in the context of dental implantology (Miyamoto et al., 2012). When bone graft, calcium phosphate ceramic and bioglass are used, relatively important healing time (four to nine months) is needed to allow bone remodeling and to secure implant insertion (Brook and Hatton, 1998, Larsson et al., 2012), while modern dental implant treatments aim at a rapid strong and long-lasting attachment between implant and bone for optimal performances.
Interestingly, tricalcium silicate-based cements (TSBCs) (such as Biodentine (Koubi et al., 2012, Koubi et al., 2012)), which are used in the clinic in the context of restorative and endodontic procedures for dentinal tissue replacement (O'Brien, 2008), could be used as bone substitutes in the context of dental implantology because it combines adapted mechanical properties (Golberg et al., 2009, Sawyer et al., 2012), biocompatibility (Camilleri et al., 2012, Leiendecker et al., 2012), with bioactive properties (Laurent et al., 2008, Laurent et al., 2012, Koubi et al., 2012, Koubi et al., 2012). Another advantage of Biodentine lies in the relatively low duration necessary to prepare the mixture before application (only 9–12 min; Golberg et al., 2009; are necessary for material preparation), thus rendering its clinical use relatively easy. TSBC are adapted to be used as bone substitute material in the context of dental implantology because of their adhesive properties with calcified tissues (Kenny and Buggy, 2003), which increase as a function of time due to their chemical composition (Watanabe et al., 2006). Beside adapted adhesive and elastic properties, bone substitute materials must also have adapted fatigue behavior (Davidson, 2006, Wong et al., 2011) in order to sustain actual biomechanical solicitations. However, the fatigue behavior of TSBC in the presence of mechanical stresses generated by dental implants remains unexplored due to the difficulty of measuring the evolution of mechanical properties of materials around the implant interface. A better understanding of the evolution of the cement biomechanical properties around the implant surface could lead to a better conception of bone graft substitute materials.
Different methods have been developed in the past to monitor the evolution of material properties around a dental implant. Dental surgeons use empirical methods based on palpation and patient sensation (Krafft et al., 2012) but these methods suffer from a lack of precision and standardization. Histomorphometry is the gold standard to assess osseointegration and stability of an implant (Franchi et al., 2007), but it is a destructive method and cannot be used to assess mechanical properties. Classical radiography (Frederiksen, 1995) and X-ray microcomputed tomography (Akca et al., 2006) have been suggested for the evaluation of the implant fixture, but resolution problems due to diffraction phenomena (Shalabi et al., 2007) around the implant interface prevent from using X-ray based approaches to measure the interface properties, which is the important parameter for the success of the surgical intervention. The Periotest (Bensheim, Germany) (Schulte et al., 1983) and Osstell (Gothenburg, Sweden) (Meredith et al., 1997) methods are biomechanical approaches clinically used for the assessment of implant stability. However, Periotest (Aparicio et al., 2006) and Osstell (Pattijn et al., 2007) measurements are dependent on the orientation and the fixation of the devices, leading to reproducibility limitations that may prevent from reliable quantitative evaluation of implant stability. More recently, an alternative nondestructive method based on the ultrasonic response of the implant has been developed by our group to assess the biomechanical properties around the implant (de Almeida et al., 2007, Mathieu et al., 2011a, Mathieu et al., 2011b). Ultrasonic techniques have the advantage to be sensitive to the bone-implant interface properties (Mathieu et al., 2011b, Mathieu et al., 2011b, Mathieu et al., 2012a, Mathieu et al., 2012b, Mathieu et al., 2012c).
The aim of this study is to investigate the evolution of the ultrasonic response of an implant embedded in TSBC and subjected to fatigue stresses. The variation of the implant ultrasonic response could lead to important information on the evolution of the biomaterial biomechanical properties around the implant.
Section snippets
Sample preparation
Fig. 1 describes the experimental set-up. BiodentineTM (Septodont, Saint-Maur-des Fossés, France) is introduced in a 8 mm diameter, 14 mm deep cylindrical hole machined in PMMA after its preparation under clinical conditions. The cement paste is obtained by mixing the commercial Biodentine powder with an increased volume of the liquid part in order to reach a very fluid material which can be easily inserted inside the mold cavity. Then, the implant is carefully inserted in liquid Biodentine so
Results
Table 1 shows the variation of the minimum, maximum, mean and standard deviation of the values of the indicator I at different times after being embedded in Biodentine without any mechanical solicitation of the implant. The results show no significant effect of time on the value of the indicator I (p=0.78, F=0.56).
Fig. 6 shows the variation of the mean values of I as a function of fatigue time for all implants. Fig. 6 also shows the linear regression line of the variation of the mean value of I
Discussion
To the best of our knowledge, this is the first study investigating the variation of the ultrasonic response of a dental implant as a function of its environment. The approach described herein can be compared with other published works. Ultrasound methods have been used previously in the domain of dental implantology to analyze bone biomechanical properties (Klein et al., 2008) prior to implant insertion. Acoustic emission was used in order to monitor the primary stability of dental implants (
Conclusion
An ultrasonic device was used to monitor changes of the ultrasonic response of a dental implant inserted in Biodentine and subjected to mechanical fatigue. An indicator I was derived based on the analysis of the amplitude of the rf signals obtained. The values of the indicator I stay constant between 48 and 72 h after implant insertion without mechanical solicitation, while I increases significantly when mechanical fatigue is applied. The increase of I is due to the debonding of the
Conflict of interest statement
There is no conflict of interest of any kind.
Acknowledgments
This work has been supported by the French National Research Agency (ANR) through EMERGENCE program (Project WaveImplant no. ANR-11-EMMA-039).
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