Validation of a new meniscal root repair technique that will be biomechanically superior to current gold standard procedures and, at the same time, will allow controlled adjustable fixation. Medial and lateral meniscus from 10 porcine knees were collected. An iatrogenic posterior root tear was created and a single transosseous tibial tunnel technique that closely replicates the repair procedure with a 2-mm-wide-knottable braided tape was performed. Randomly, in one group (A) two simple cinch stitch were applied to suture the posterior root of the meniscus and, in the other group (B), a simple stich that holds the meniscus in two points in a crosse match configuration was used. For final fixation, alternating surgeon's knots (A group) and a doubled suture knot that allows an adjustable fixation were used (B group). All repairs were standardized for location and the repair stiches were placed in the body of the meniscus. The new suture configuration (B group) showed a better biomechanical performance in terms of load for both the medial [151,0-560,3] 306,9±173,8N and the lateral posterior root fixation [268,2-463,1] 347,4±74,3N in comparison to the cinch stitch (A group) [219,0-365,2] 268,9±58,7N and [219,0-413,6] 318,0±72N. The maximum stiffness was also higher for the new tested suture configuration (B group) for both the medial meniscus [10,6-34,5] 18,9±9,2N/mm vs [7,1-12,7] 10,9±2,2N/mm and the lateral meniscus [16,0-27,9] 21,6±5,5N/mm vs [7,6-15,6] 12,6±3,5N/mm. The presented new meniscal root repair is biomechanically superior to current gold standard techniques, as the cinch stich made with tape, keeping the simplicity and reproducibility of the procedure and, at the same time, is economically advantageous since a single tape in needed and allows adjustable fixation of the repair over a button.
The patients with a total hip arthroplasty is growing in world manly in Europe and USA, and this solution present a high success at 10years in several orthopaedic registers. The application of total press-fit hip fixation presents the most used solution, but presents some failures associated to the acetabular component fixation, associated to the load transfer and bone loss at long term. The aim of this work is to investigate the influence of different acetabular bone loss in the strain distribution in iliac bone. To evaluate implant fixation, an experimental study was performed using acetabular press-fit component simulating different acetabular bone loss and measuring the strain distribution. The experimental samples developed was based in an iliac bone model of Sawbones supplier and a acetabular component Titanium (Stryker) in a condition press-fit fixation and was implanted according surgical procedure with 45º inclination angle and 20º in the anteversion angle. Were developed five models with same initial bone, one with intact condition simulating the cartilage between bones and four with different bone loss around the acetabular component. These four models representing the evolution of bone support of acetabular components presented in the literature. The evolution of bone loss was imposed with a CAD CAM process in same iliac bone model. The models were instrumented with 5 rosettes in critical region at the cortical bone to measure the strain evolution along the process.Introduction and Objective
Materials and Methods
The ankle cartilage has an important function in walking movements, mainly in sports; for active young people, between 20 and 30 years old, the incidence of osteochondral lesions is more frequent. They are also more frequent in men, affecting around 21,000 patients per year in USA with 6.5% of ankle injuries generating osteochondral lesions. The lesion is a result of ankle sprain and is most frequently found in the medial location, in 53% of cases. The main objective of this work was to develop an experimental and finite element models to study the effect of the ankle osteochondral lesion on the cartilage behavior. The right ankle joint was reconstructed from an axial CT scan presenting an osteochondral lesion in the medial position with 8mm diameter in size. An experimental model was developed, to analyze the strains and influence of lesion size and location similar to the patient. The experimental model includes two cartilages constructed by Polyjet™ 3D printing from rubber material (young modulus similar to cartilage) and bone structures from a rigid polymer. The cartilage was instrumented with two rosettes in the medial and lateral regions, near the osteochondral region. The fluid considered was water at room temperature and the experimental test was run at 1mm/s. The Finite element model (FE) includes all the components considered in the experimental apparatus and was assigned the material properties of bone as isotropic and linear elastic materials; and the cartilage the same properties of rubber material. The fluid was simulated as hyper-elastic one with a Mooney-Rivlin behavior, with constants c1=0.07506 and c2=0.00834MPa. The load applied was 680N in three positions, 15º extension, neutral and 10º flexion.Introduction
Materials and Methods
Total shoulder arthroplasty is a well-tested procedure that offers pain relief and restores the joint function. However, failure rate is still high, and glenoid loosening is pointed as the main reason in orthopedic registers. In order to understand the principles of failure, the principal strain distributions after implantation with Comprehensive® Total Shoulder System of Biomet® were experimental and numerically studied to predict bone behavior. Fourth generation composite left humerus and scapula from Sawbones® were used. These were implanted with Comprehensive® Total Shoulder System (Biomet®) with a modular Hybrid® glenoid base and Regenerex® glenoid and placed in situ by an experienced surgeon. The structures were placed in order to simulate 90º abduction, including principal muscular actions. Muscle forces used were as follows: Deltoideus 300N, Infraspinatus 120N, Supraspinatus 90N, Subscapularis 225N. All bone structures were modeled considering cortical and the trabecular bone of the scapula. The components of prosthesis were placed in the same positions than those in the in vitro models. Geometries were meshed with tetrahedral linear elements, with material properties as follows: Elastic modulus of cortical bone equal to 16 GPa, elastic modulus of trabecular bone equal to 0.155 GPa, polyethylene equal to 1GPa and titanium equal to 110 GPa. The assumed Poisson's ratio was 0.3 in all except for polyethylene where we assumed a value of 0.4. The prosthesis was considered as glued to the adjacent bone. The finite element model was composed of 336 024 elements. At the glenoid cavity, the major influence of the strain distributions was observed at the posterior-superior region, in both cortical and trabecular bone structures. The system presents critical region around holes of fixation in glenoid component. At the trabecular bone, the maximum principal strains at the posterior-superior region ranged from 2250 µε to 3000 µε. While at the cortical bone, the maximum principal strains were 300 µε to 400 µε. The results observed evidence some critical regions of concern and the effect of implant in the bone strains mainly at the posterior-superior region of the glenoid cavity is pronounced. This indicates that this region is more affected by the implant if bone remodeling is a concern and it is due to the strain-shielding effect, which has been connected with loosening of the glenoid component.
The Temporomandibular joint (TMJ) is a complex and important joint for daily activities, and the alloplastic implant is recommended as the best solution, after repeated surgeries, failed autogenous grafts, highly inflammatory metabolic arthritis, fibrous or bony ankyloses. Some complications in total TMJ replacement are associated with implant design, screw fixation failure, implant displacement, fibrous tissue formation, (Speculand, et al. 2000). Some numeric studies evaluate the number of screws needed to guarantee the good fixation and suggest a minimum of three (Ramos et al. 2015), but is a controversy conclusion. The Biomet Microfixation TMJ stock prosthesis, Jacksonville, FL, USA is one of the three or four in the market. Clinical studies published by this device between 2005 and 2015 indicate a success rate of around 84 to 91% with improvements in mouth opening, a decrease in pain score and improved quality of life. The present study analyses experimentally the load transfer of this device. The intact, clean cadaveric ramus was instrumented with four rosettes model (KFG-1-120-D17-11 L3M2S, by Kywoa Electronic Instruments Co™, Japan), one in lateral region, two in lateral region and one in lingual face. The condyle was loaded with the temporal reaction; the load was applied constant velocity of 1mm/min in three continuum phases and with three stops at 100N, 200N and 300N. Next, the Biomet microfixation implant was fixed to the same cadaveric mandibular ramus after resection. The implant was 50mm in length. It was fixed with five 6AL/4V Titanium self-tapping screws with 2.7mm diameter were long enough to establish a bi-cortical support. The screws were screwed into the bone with a torque-screwdriver a constant torque of 0.2Nm. The same rosettes were analyzed before and after implantation and the mandible displacement two. The experimental results for the mandibular ramus present a linear behavior up to 300N load in condyle, with the Biomet implant influencing strain distribution; the maximum influence was near the implant (rosette #4) is around 59%. The average vertical displacement of the mandibular ramus (300N) was measured by machine: 1.18 (±0.02) mm for the intact mandibular ramus and 1.21 (±0.02) mm for the implanted one, which represents a 2.8% differences between the experimental models and reduce of stiffness. The maximum principal strain deformation was observed in the rosette #3 with 1360µε more 20% than the intact mandible for 300N of reaction. The experimental results show that the Biomet TMJ mandibular ramus implant changes the load transfer in the ramus, compared to the intact, with its strain shielding effect. The results indicate the minimum number of screws is three to guarantee a good load transfer but the surface preparation of condyle presents an important factor.
Positioning of the hip resurfacing is crucial for its long term survival and is critical in young patients for some reasons; manly increase the wear in the components and change the load distribution. THR have increased in the last years, mainly in young patients between 45 to 59 years old. The resurfacing solution is indicated for young patients with good bone quality. A long term solution is required for these patients to prevent hip revision. The resurfacing prosthesis Birmingham Hip Resurfacing (BHR) was analyzed in the present study by in vitro experimental studies. This gives indications for surgeons when placing the acetabular cup. One synthetic left model of composite femur (Sawbones®, model 3403), which replicates the cadaveric femur, and four composite pelvic bones (Sawbones®, model 3405), were used to fix the commercial models of Hip resurfacing (Birmingham model). The resurfacing size was chosen according to the head size of femurs with 48 mm head diameter and a cup with 58 mm. They were introduced by an experimented surgeon with instrumental of prosthesis. The cup is a press fit system and the hip component was cemented using bone cement Simplex, Stryker Corp. The acetabular cup was analyzed in 4 orientations; in anteverion with 15º and 20°; and in inclination 40 and 45°. Combinations of these were also considered The experimental set-up was applied according to a system previously established by Ramos When the femur was instrumented with three rosettes in medial, anterior and posterior aspect, the maximum strain magnitude was observed in the medial aspect of femur with a minimum principal strain of −2070µε for 45° inclination and 20° of anterversion. The pubic region was found most critical region after instrumenting the Iliac bone with four rosettes, with a minimum principal strain around −2500µε (rosette 1), for the 45° inclination and 20° of anterversion. We have observed the great influence of the inclination on the strain distribution, changing its magnitude from compression to traction in different bone regions. The minimum principal strain is more critical in medial aspect of the femur and the influence of strain is about 7% when orientation and inclination change. The maximum influence was observed in the anterior aspect, where the anteversion presents a significant influence. The results show the interaction between inclination and anterversion in all aspects, being observed lower values in lower angles. The orientation of the acetabular cup significantly influences the strain distribution on the iliac surface. Besides, as anterversion increases, more strains are induced, mainly in the region of iliac body (rosette 3).
