Examination of efferent lymph nodes after 2 years of transcortical implantation of poly(L-lactide) containing plugs: a case report.
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Animals↗
Biomedical subjects
K de Groot
Publications and source records attributed to K de Groot.
Dissolution and scanning electron microscopic studies of Ca,P particle-containing bioactive glasses.
Calcium phosphate (Ca,P) precipitation behavior on the surface of two bioactive glasses and four bioactive glass composites--two with hydroxylapatite (Ca10(PO4)6 (OH)2) and two with rhenanite (CaNaPO4)--were studied in simulated body fluid (SBF) and in Tris-Buffer at 5, 8, 16, 24, 48, 72, and 144 h. The weight loss of the materials was measured and the amount of precipitation was estimated using scanning electron microscopy with electrochemical detection (SEM-EDX) analysis. The test was repeated for one glass and its respective rhenanite composite every 3 h until 60 h and thereafter every 10 h until 150 h in SBF. Atomic absorption spectroscopy, spectrophotometry, SEM-EDX analysis, and pH measurements were performed on these samples. It is shown that in vitro the composite materials have a higher capacity for Ca,P precipitation than the glasses. Weight losses of the materials correlate well with their composition. Both the glass and Ca,P phases influence the precipitation mechanism and rate. Precipitation begins preferably from the glass phase. Ca,P particles clearly influence the time of onset and rate of precipitation. Cross-sectional EDX analysis of the samples revealed an absence of a clear Si-rich layer in glass A0B0 (SiO2 53.9 mol %, Na2O 27.5, CaO 12.4, P2O5 6.2, Al2O3 0.0 and B2O3 0.0) composites. This was attributed to the presence of extra calcium and phosphate ions on the surface of the material. The ion-concentration and pH change curves offered insight into the mechanism of precipitation. A connection was established between SEM-EDX results and the release curves. Formation of an Si,Ca,Na film was observed that seemed to initiate the Ca,P precipitation.(ABSTRACT TRUNCATED AT 250 WORDS)
Biocompatible Materials↗
Calcium phosphate formation within sol-gel prepared titania in vitro and in vivo.
Calcium phosphate formation is induced within sol-gel prepared titania and grows toward a calcium phosphate solution in which the titania is immersed. The implantation of this sol-gel prepared titania film coating on TiA16V4 core into the femurs of goats shows an accumulation of calcium phosphate within the titania film 12 weeks postoperatively, which leads to the connection of the titania film coating to the bone. Therefore, sol-gel prepared titania is probably bioactive. The results indicate that hydrated titania gel is able to generate calcium phosphate by intake of calcium and phosphate from the surrounding solution. Sufficient TiOH concentration at the titania surface is needed to start this process. Titanium could be bioactive, if its hydrolysis can be accelerated.
Animals↗
Local residual ridge augmentation with solid hydroxyapatite blocks: Part I--An animal experiment.
Twenty-four implants were placed in the jaws of five dogs for evaluation of the possibility of correcting local resorption. Implants and surrounding tissues were evaluated clinically, radiographically, and histologically for periods of 3 to 24 months. The implants were clinically and radiographically stable. Some were surrounded by connective tissue fibers and others were bonded to underlying cortical bone.
Alveolar Bone Loss↗
Local residual ridge augmentation with solid hydroxyapatite blocks: Part II--Correction of local resorption defects in 50 patients.
Replacement of anterior teeth with fixed or removable prostheses is often a compromise, because the resorbed residual ridge in the area of missing teeth cannot be ideally restored functionally and esthetically at the same time. To address this problem, 67 blocks of hydroxyapatite were placed subperiosteally to improve residual ridge resorption defects subsequent to loss of anterior teeth in 50 patients. The implants were evaluated clinically and radiographically for 6 months to 7 years after implantation. Results indicate that the suggested approach improves the esthetic results and the prognosis of fixed prostheses.
Adolescent↗
Adherence to a metal, polymer and composite by Staphylococcus aureus and Staphylococcus epidermidis.
Bacterial adherence on to several materials with a potential application in reconstructive surgery was studied. Polymer (poly(L-lactide)), composite (hydroxyapatite/poly(L-lactide)) and metal (316L stainless steel) were evaluated both as smooth and sandblasted specimens. All materials were incubated in phosphate-buffered saline, challenged with Staphylococcus aureus or S. epidermidis and evaluated for up to 24 h. S. aureus showed a preference for the metal and composite tested over the polymer used. For S. epidermidis no preference was found for one of the investigated materials. The influence of surface roughness on bacterial growth was demonstrated by increased colonization on the sandblasted specimens.
Bacterial Adhesion↗
Induction and morphology of hydroxyapatite, precipitated from metastable simulated body fluids on sol-gel prepared silica.
Hydroxyapatite crystallization is induced at 37 degrees C by sol-gel prepared silica from metastable calcium phosphate solutions. The morphology of the apatite forming on the silica surface depends on the nature of the solutions. For example, apatite grew in a flake-like form at pH 7.4. The morphology changed to plate-like when the pH was adjusted to pH 7.2. At this lower pH, the apatite plate even exhibited a hexagonal feature, reflecting the unique hexagonal structure of hydroxyapatite. An increase in either Mg or P ion concentration of the fluid can cause apatite to grow in a rod-like shape while addition of F ions to the fluid leads to a perfect needle pattern. The flake geometry of apatite was not altered by increasing Ca concentration from 2.5 to 3.8 mM in the solution. From this we conclude that sol-gel prepared silica is an efficient apatite inducer and the morphology of the hydroxyapatite deposit is determined by factors of the fluid such as pH, Ca/P molar ratio, Mg and F concentrations.
Body Fluids↗
Relationship between the colour change of hydroxyapatite and the trace element manganese.
Hydroxyapatite containing the trace element manganese turns blue after sintering at high temperature in an oxidizing atmosphere. This phenomenon is related to the oxidation of manganese ions in the special crystal structure of hydroxyapatite. Combination of the crystal structure with electron spin resonance spectra gives an explanation for this oxidation of Mn2+ ions at Ca(l) sites into Mn5+ ions and the formation of MnO4(3-) ions at PO4(3-) sites, corresponding to the colour change of hydroxyapatite.
Calcium↗
Application of magnetron sputtering for producing ceramic coatings on implant materials.
Radiofrequent magnetron sputtering was used to produce calcium phosphate coatings on metal and plastic substrates. Scanning electron microscopy showed that the deposited films had a uniform thickness and a dense columnar structure. Energy-dispersive X-ray analysis, X-ray crystal diffraction and atomic absorption spectrometry demonstrated that the sputtered layer was well-crystallized calcium phosphate ceramic with a Ca/P ratio varying between 1.9 and 2.5. The biocompatibility of the coatings was determined by in vitro and in vivo experiments. It was found that the coatings were biocompatible without any sign of adverse tissue reaction. It was concluded that magnetron sputtering is a promising method for forming a biocompatible ceramic coating onto an implant material. Nevertheless, several problems have to be solved before magnetron sputtering can be used on a routine basis for the production of Ca/P coatings.
Animals↗
Tensile strength of the interface between hydroxyapatite and bone.
Tensile strength of the interface between hydroxyapatite (HA) and bone was tested. Scanning electron microscopy was used to observe the tensile failure mode and the morphological change of hydroxyapatite ceramic surface in bone. The porosity of hydroxyapatite is 14% and pore size less than 2 microns. After 2 weeks of implantation, the tensile strength of the interface is 0.72 MPa. After 4, 8, and 16 weeks, the average tensile strength stayed at 1.5 MPa. SEM showed that tensile failure occurred at the HA-bone interface at the second week, but after 4 weeks, the failure occurred between HA particles within the bulk, and not at the HA-bone interface. Calcified tissue was directly deposited on the HA ceramic surface and exits also in the micropores. Near the interface, sintered necks among HA ceramic particles were subjected to biodegradation.
Animals↗
A finite element analysis of the push-out test: influence of test conditions.
The commonly used method for quantitative evaluation of the strength of a bone-implant interface is the push-out test. In order to give an impulse to standardization and to gain more insight in the biomechanics of the push-out test, a finite element analysis of this test was performed. This study focused on the influence of test conditions on the push-out results. The influence of the following four parameters on the interface stress distribution was tested: (a) clearance of the hole in the support jig, (b) Young's modulus of the implant; (c) cortical thickness; and (d) implant diameter. The distance between the implant and the support jig turned out to be very critical for the occurrence of peak stresses in the interface. Variations of the Young's modulus of the implants resulted in a wide range of interface shear stresses. Variation of the cortical thickness showed a reciprocal relationship between cortical thickness and interface shear stress. However, the interface stress distribution remained uniform under the specific test circumstances. These findings also hold for variations in implant diameter. The present investigation shows that the clearance of the hole in the support jig, and the Young's modulus of the implant are parameters which most strongly influence the interface stress distribution. The clearance of the hole in the support jig is the most critical parameter, but also the parameter that can be controlled most easily. Lack of standardization with regard to these parameters can lead to uninterpretable test results. It is recommended that the clearance of the hole in the support jig is at least 0.7 mm and that push-out results are only compared with each other when materials with similar Young's modulus are concerned.
Animals↗
Preparation of dense hydroxylapatite or rhenanite containing bioactive glass composites.
The effect of time at 600 degrees C and of small additions of Al2O3 and B2O3 on the sintering of two composite materials of (1) hydroxylapatite (Ca10(PO4)6(OH)2) and bioactive glass (SiO2-CaO-P2O5-Na2O) or (2) rhenanite (CaNaPO4) and bioactive glass were studied. Scanning microscopy, quantitative EDX, x-ray diffraction, helium gas density measurements, and diametral measurements were performed on the resulting composites. No reactions were observed with the SEM or XRD between the hydroxylapatite particles and the glass matrix within sufficient sintering times to achieve maximum density. The rheunanite-containing composites were observed to form Na2O2CaO3SiO2 crystals by x-ray diffraction, probably as a result of dissolution of the rhenanite particle surfaces into the glass phase, the crystals formed in the glass or at the interface of the glass, and the ceramic particles. However, within the short sintering times needed to achieve maximum density the rhenanite particles remained mostly intact. The rhenanite-containing materials gave better results than the hydroxylapatite-containing materials. The glass composition had a great effect on the densification process.
Biocompatible Materials↗
Evaluation of hydroxylapatite/poly(L-lactide) composites: mechanical behavior.
By mixing hydroxylapatite (HA) into L(-)-dilactide monomer, prior to polymerization to poly(L-lactide) (PLLA), hydroxylapatite filled poly(L-lactide) composites were obtained. This study reports about the mechanical properties of these composites compared with unfilled PLLA. It was concluded that a 30 wt% HA/PLLA composite has better compressive and tensile strengths, higher stiffness and Vickers hardness number than unfilled PLLA (Mv: 125-150,000). Gas sterilization (ethylene oxide) affects molecular weight and flexural strength significantly. Implantation studies revealed loss of 50% of initial flexural strength within 3 weeks, and a faster decline of flexural strength was observed in phosphate buffered saline than in the subcutis of goats. From a mechanical point of view storage at -20 degrees C proved to be a safe method. In its current state HA/PLLA composites can not be used as implant materials that have to resist major forces. However, such composites might be useful in non-loadbearing applications in orthopedic or maxillofacial surgery.
Animals↗
The ultrastructure of the bone-hydroxyapatite interface in vitro.
Rat bone marrow cells were cultured on plasma-sprayed hydroxyapatite (HA). The cells formed a mineralized extracellular matrix (ECM) that exhibited several characteristics of bone tissue. The interface between this mineralized ECM and the HA was studied at the ultrastructural level with scanning and transmission electron microscopy and x-ray microanalysis. Initially, the deposition of a globular, afibrillar matrix was observed on HA. This was followed by the integration of collagen fibers in this matrix and their subsequent mineralization. At the bone-HA interface two distinctly different interfacial structures were observed. An electron-dense layer with a thickness of 20-60 nm was regularly present, which contained both organic and inorganic material and was rich in glycosaminoglycans. The interfaces differed however, in the presence or absence of an amorphous zone which was free of collagen fibers and had an average thickness of 0.7-0.8 microns. It was frequently seen interposed between the electron-dense layer and the hydroxyapatite. Similar interfacial structures have also been described in the in vivo environment, where they were referred to as lamina limitans-like or cement linelike. From the results of this study, it can be concluded that the described in vitro system is a suitable model to study bone-biomaterial interactions.
Animals↗
Behaviour of fetal rat osteoblasts cultured in vitro on bioactive glass and nonreactive glasses.
We examined the behaviour of fetal rat osteoblasts cultured upon bioactive glass and nonreactive glasses, and the supposed stimulatory effects of bioactive glass on osteoblasts. Nonreactive glass cultures showed flattened cells with almost no dorsal ruffles. Bioactive glass cultures showed compact cells with dorsal ruffles and filapodia resulting in the formation of a denser cell layer. For confluent nonreactive glass cultures the osteoblast expression was mainly concentrated in the clustered cells which were formed upon the monolayer, whereas for confluent bioactive glass cultures the osteoblast expression was more generally distributed. The production of type I collagen, osteocalcin and an osteoblast-specific antigen was shown by immunocytochemistry for all cultures, although differences in distribution were observed. The bioactive layer of bioactive glass is responsible for a better osteoblast-like morphology, a higher proliferation rate and generally a better osteoblast expression.
Alkaline Phosphatase↗
Soft tissue response to different types of sintered metal fibre-web materials.
Recently, it has been demonstrated that the soft tissue response to polymeric filter implants was predominantly dependent on the implant surface topography and that variation in the implant material had little effect. The purpose of this study, therefore, was to compare histologically the soft tissue response to sintered fibre-web implants made from different materials and with varying web porosity. Three different fibre-web materials with two different weights and two different porosities were used. The implants were inserted subcutaneously in the dorsum of rabbits. The implants were left in situ for 4 and 12 wk. Histological and tissue compatibility evaluations were performed. It is found that all the tested fibre-web materials show a good biocompatible behaviour. In addition, the results appear to indicate a relation between flexibility of an implant material and tissue behaviour.
Adipose Tissue↗
Cellular reaction on the intraperitoneal injection of four types of polylactide particulates.
Four types of polylactide particulates, P-L-LA 100, 250, 550 KD and a P-DL-LA 400 KD were injected into the peritoneal cavity of mice. The inflammatory reaction showed an increase in cell number (mainly neutrophilic granulocytes) up to 48 h after which the cell numbers decreased below the control (phosphate-buffered saline). All four polylactide particulates aggregated and intermingled with inflammatory cells. The aggregates remained throughout the investigation period of 6 months. Quantitative measurements showed that standardization of the particle form and size is essential. From this study and other experiments in which calcium phosphates and asbestos were injected intraperitoneally, it is concluded that the inflammatory response observed in the peritoneal cavity is related to the type of material injected and probably to form and size of the individual particles, but not to molecular weight.
Animals↗
Intramedullary fixation with screwed, conical stems--unsolicited results from animal experiments.
For the purpose of studying bone remodeling around prostheses, a segmental replacement for the goat tibia was designed, using a conical, screw-threaded, hydroxyapatite-coated stem for fixation. Eight goats were provided with the implant, seven of which loosened within 10 days post-operatively, displaying progressive radiolucency and gross rotational motion. The eighth one also loosened radiographically, but developed a stabilizing callus bridge to prevent motion. A second design of similar shape and coating, but lacking the screw threads, was designed and also applied in eight animals. In this case, no loosening occurred in the first 6 weeks post-operatively. It is concluded that the application of screwed intramedullary stems for prosthetic fixation is not a viable concept, because the threads prevent the stem from subsiding and restabilizing when minor initial interface stress-relaxation and remodeling has occurred.
Animals↗