Osseointegration of 3D porous and solid Ti–6Al–4V implants - Narrow gap push-out testing and experimental setup considerations

Frosch, Stephan; Nüsse, Verena; Frosch, Karl‐Heinz; Lehmann, Wolfgang; Buchhorn, Gottfried

doi:10.1016/j.jmbbm.2020.104282

Cited by 13 publications

(13 citation statements)

References 43 publications

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“…The average maximum push-out force obtained from HR-Ti, Gel/HA/HR-Ti and Gel/ALN-HA/HR-Ti are 159.7 N, 426.2 N and 530.7 N, respectively. The pushout force of Gel/ALN-HA/HR-Ti is significantly higher than the Ti based implants reported in the previous literature (e.g., ~174N, [50] ~200N, [21] ~480N [51] ).…”

Section: In Vivo Osteointegrationcontrasting

confidence: 55%

3D Printed Multi Functional Ti6Al4V Based Hybrid Scaffold for the Management of Osteosarcoma

Cai¹,

Huang²,

Wang³

et al. 2021

Preprint

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2.1.1 Preparation of drug-laden Gel/HA composite Alendronate (ALN), is a commonly used bisphosphonate drug for osteoporosis management and bone regeneration. [33] However, direct loading of ALN onto Gel often results in burst drug release due to the fast Gel degradation in vivo. In contrast, degradable HA microsphere is an excellent drug delivery vehicle, which can provide sustained/controlled drug release as well as promoting osteoblasts mineralization/maturation (due to slow release of Ca2+ and PO43-). [34] To prepare the ALN-laden HA microspheres/Gel composite (ALN-HA/Gel), HA microspheres were first synthesized following established procedure. [35] 0.5 g ALN was then added into 50 mL aqueous dispersion containing 2.0 g HA microspheres. After mixing using shaking incubator under 37 ℃ for 48 h, ALN-HA were collected by centrifugation and vacuum dried at 40 ℃ for 24 h. ALN concentration in the supernatant solution was evaluated by UV-vis spectroscopy. The drug-laden Gel/ALN-HA can be obtained by dispersing 3.0g ALN-HA microspheres in 50 mL deionized water, followed by addition of 8.0 g Gel, and stirred magnetically at 1000 rpm under 50 ℃ for 1 h. 2.1.2 Preparation of 3D printed Ti6Al4V scaffolds 3D printed Ti6Al4V scaffolds (named as Ti) were manufactured by electron beam melting (EBM) facility in-house. The lattice structure was designed by computer-assisted design (CAD) software (Magics, Materialise, Belgium) based on a dodecahedron unit cell with strut diameter of 300 μm and porosity of 80%. Cubic scaffolds (5mm × 5mm × 5mm) were used for in vitro testing and cylindrical scaffolds (Φ = 6mm, height = 6mm) were used for in vivo experiments. All samples were thoroughly cleaned by sonication in acetone, alcohol and deionized water for 30 min, respectively. The Ti scaffolds were subsequently subjected to hydrothermal treatment. [36] Specifically, the scaffolds were immersed in an aqueous solution (m(H2O2):m(H3PO4) 9:1) and placed in a Teflon-lined autoclave under 220 ℃ for 24 h. After the treatment, scaffolds were washed with distilled water and dried in air at room temperature for 24 h. The hydrothermally treated samples were named as HR-Ti. 2.1.3 Preparation of Gel/ALN-HA infused HR-Ti scaffold The Gel/ALN-HA mixture was infused into the HR-Ti, then the infused scaffolds were held at -80<a> </a>℃ overnight followed by freeze-drying at -40 ℃ for 48 h. After that, the infused scaffolds were immersed in 100 mL ethanol containing 50mmol/L 1-ethyl-3-(3- (dimethylamino) propyl) carbodiimide hydrochlorid (EDC∙HCl) and N-hydroxysuccinimide (NHS) at 4 ℃ for 10 h to crosslink the Gel content. Afterwards, the scaffolds were washed three times by ethanol and freeze-dried again. The final scaffolds were named as Gel/ALN-HA/HR-Ti. For comparison, ALN/HR-Ti (without Gel and HA), Gel/ALN/HR-Ti (without HA) and Gel/HA/HR-Ti (without ALN) were also prepared.

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Section: In Vivo Osteointegrationcontrasting

confidence: 55%

3D Printed Multi Functional Ti6Al4V Based Hybrid Scaffold for the Management of Osteosarcoma

Cai¹,

Huang²,

Wang³

et al. 2021

Preprint

View full text Add to dashboard Cite

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“…After 12 weeks, the mid-term osseoremodeling, which represents an adaptation of the bone formation to the load direction, is predominantly developed. Histologically, we now expect mostly lamellar bones and a reduced presence of osteoid as well as a stronger bony anchoring ( [8] ; [15 , 34] ). As a result, disorders of short-term osseohealing and mid-term osseoremodeling can be identified separately [5 , 25] .…”

Section: Animal Modelmentioning

confidence: 95%

“…The ideal implantation site for implants in the presented rabbit model certainly depends on the intended implant design and function as well as scope of application in humans. For use as a trabecular bone substitute, we have made the following considerations for implant positioning ( [15] ): (a) transchondral placement with probable gap formation may result in penetration of lubricant from the joint space into the interface [3] ; (b) intramedullary placement or intra diaphyseal (axial) result in a large contact area with the endosteum and marrow; this probably fails to establish complete surface contact to the bone due to the conical shape mismatch leading to erroneously lower data [3 , 10 , 26] ; (c) exclusive intracortical contact neglects on-growth of cancellous bone [4 , 5 , 22 , 33] ; (d) intracondylar placement, as presented in this study, provides cortical and cancellous contact and strains applied to the cylinders [29 , 30] .…”

Section: Animal Modelmentioning

confidence: 99%

“…We felt that a cylindrical implant would at least deflect the direction of load. The study arrangements presented here are based on our previous biomechanical push-out study ( [15] ). Test implants of the same size with different structural properties (solid vs. porous) were compared with regard to their osseointegrative ability ( Fig.…”

Section: Biomechanical Test Arrangementmentioning

confidence: 99%

“…In order to keep these deviations as low as possible, certain conditions and principles for the animal model and test arrangements should be adhered to as far as possible in order to improve the measurement accuracy and make the results more comparable. We previously submitted titanium alloy implants to a comparative biomechanical push-out study using an animal model to investigate the influence of different structure properties on osseointegration ( [15] ).…”

Section: Introductionmentioning

confidence: 99%

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Considerations on the animal model and the biomechanical test arrangements for assessing the osseous integration of orthopedic and dental implants

Frosch

Buchhorn

2021

MethodsX

Self Cite

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In implant research, a central objective is to optimize the osseous integration of implants according to their function and scope of application. In the preclinical stage, the animal model is commonly used to study implants for in vivo host tissue response and biomechanical tests are a frequently applied method for characterization of contact phenomena. However, the individual parameters and options for both the animal model and the biomechanical test arrangements vary widely, which can negatively affect the reliability and comparability of the results. In the present method description, we focus on implants for trabecular bone replacement and outline differentiated considerations for optimizing the animal model and the biomechanical test arrangement best suited for the area of application described. In addition, our aim was to present an optimized and strict study protocol for biomechanical push-out tests and step-by-step instructions in order to achieve precise and comparable results. The rabbit model and the distal femur as an implantation site are ideal for biomechanical assessment of implant osseointegration. Push-out tests are recommended, in which conformity of the axis is mandatory. Sequential examination periods are beneficial, e.g. after 4 weeks for osseohealing and after 12 weeks for osseoremodeling.

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Calibration of Aseptic Loosening Simulation for Coatings Osteoinductive Effect

Baroni,

Oliviero,

La Mattina

et al. 2024

Ann Biomed Eng

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The risk of aseptic loosening in cementless hip stems can be reduced by improving osseointegration with osteoinductive coatings favoring long-term implant stability. Osseointegration is usually evaluated in vivo studies, which, however, do not reproduce the mechanically driven adaptation process. This study aims to develop an in silico model to predict implant osseointegration and the effect of induced micromotion on long-term stability, including a calibration of the material osteoinductivity with conventional in vivo studies. A Finite Element model of the tibia implanted with pins was generated, exploiting bone-to-implant contact measures of cylindrical titanium alloys implanted in rabbits’ tibiae. The evolution of the contact status between bone and implant was modeled using a finite state machine, which updated the contact state at each iteration based on relative micromotion, shear and tensile stresses, and bone-to-implant distance. The model was calibrated with in vivo data by identifying the maximum bridgeable gap. Afterward, a push-out test was simulated to predict the axial load that caused the macroscopic mobilization of the pin. The bone-implant bridgeable gap ranged between 50 μm and 80 μm. Predicted push-out strength ranged from 19 N to 21 N (5.4 MPa–3.4 MPa) depending on final bone-to-implant contact. Push-out strength agrees with experimental measurements from a previous animal study (4 ± 1 MPa), carried out using the same implant material, coated, or uncoated. This method can partially replace in vivo studies and predict the long-term stability of cementless hip stems.

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Osseointegration of 3D porous and solid Ti–6Al–4V implants - Narrow gap push-out testing and experimental setup considerations

Cited by 13 publications

References 43 publications

3D Printed Multi Functional Ti6Al4V Based Hybrid Scaffold for the Management of Osteosarcoma

3D Printed Multi Functional Ti6Al4V Based Hybrid Scaffold for the Management of Osteosarcoma

Considerations on the animal model and the biomechanical test arrangements for assessing the osseous integration of orthopedic and dental implants

Calibration of Aseptic Loosening Simulation for Coatings Osteoinductive Effect

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