A New Biphasic Dicalcium Silicate Bone Cement Implant.

Fausto Zuleta,Sergio Gehrke,José Maté-Sánchez De Val,José Calvo-Guirado,Angel Murciano,Piedad De Aza

doi:10.3390/ma10070758

Abstract

This study aimed to investigate the processing parameters and biocompatibility of a novel biphasic dicalcium silicate (C2S) cement. Biphasic α´L + β-C2Sss was synthesized by solid-state processing, and was used as a raw material to prepare the cement. In vitro bioactivity and biocompatibility studies were assessed by soaking the cement samples in simulated body fluid (SBF) and human adipose stem cell cultures. Two critical-sized defects of 6 mm Ø were created in 15 NZ tibias. A porous cement made of the high temperature forms of C2S, with a low phosphorous substitution level, was produced. An apatite-like layer covered the cement’s surface after soaking in SBF. The cell attachment test showed that α´L + β-C2Sss supported cells sticking and spreading after 24 h of culture. The cement paste (55.86 ± 0.23) obtained higher bone-to-implant contact (BIC) percentage values (better quality, closer contact) in the histomorphometric analysis, and defect closure was significant compared to the control group (plastic). The residual material volume of the porous cement was 35.42 ± 2.08% of the initial value. The highest BIC and bone formation percentages were obtained on day 60. These results suggest that the cement paste is advantageous for initial bone regeneration.

Highlights

Injectability, in situ self-setting, and biocompatibility are characteristics of bone cements, which make them encouraging materials for a wide range of clinical applications in traumatology and maxillo-facial surgery.The five main phases of Portland cement are: tricalcium silicate (Ca3 SiO5 ), dicalcium silicate (Ca2 SiO4 ), tricalcium aluminate (Ca3 Al2 O6 ), a tetracalcium alumino ferrite (Ca4 Al2 Fe2 O10 ), and a sulfate phase (CaSO4 ·2H2 O) [1]
It was obvious that the high temperature temperature αL andsilicate β dicalcium silicate peaks with no other detectable form αL and form β dicalcium peaks appeared, withappeared, no other detectable phases
Slight shift in relation to the corresponding cards is observed in the pattern, relation to the corresponding Joint Committee on Powered Diffraction Standards (JCPDS) cards is observed in the X-ray diffraction (XRD) pattern, because the phases because contain phases contain aofsmall substitution of phosphorous-forming solution

Summary

Introduction

Injectability, in situ self-setting, and biocompatibility are characteristics of bone cements, which make them encouraging materials for a wide range of clinical applications in traumatology and maxillo-facial surgery.The five main phases of Portland cement are: tricalcium silicate (Ca3 SiO5 ), dicalcium silicate (Ca2 SiO4 ), tricalcium aluminate (Ca3 Al2 O6 ), a tetracalcium alumino ferrite (Ca4 Al2 Fe2 O10 ), and a sulfate phase (CaSO4 ·2H2 O) [1]. MTA materials are presently used for many clinical applications in dentistry, including pulp. MTA materials are presently used for many clinical applications in dentistry, including pulp capping, root-perforations repair, root-end filling, and apicogenesis [4,5,6,7]. The long setting time of capping, root-perforations repair, root-end filling, and apicogenesis [4,5,6,7]. The long setting time of approximately 2 h is the main disadvantage of MTA as a dental material [8]. Bone approximately 2 h is the main disadvantage of MTA as a dental material [8] For this purpose, bone cement should ideally have a relatively short setting time to avoid being washed away by saliva and cement should ideally have a relatively short setting time to avoid being washed away by saliva and to reduce the possibility of unset material irritating oral tissues

Objectives

Methods

Results

Conclusion