Introduction. Total knee arthroplasty (TKA) implant systems offer a range of sizes for orthopaedic surgeons to best mimic the patient's anatomy and restore joint function. From a biomechanical perspective, the challenge on the TKA implants is affected by two factors: design geometry and in vivo load. Larger geometry typically means more robust mechanical structure, while higher in vivo load means greater burden on the artificial joint. For an implant system, prosthesis geometry is largely correlated with implant size, while in vivo load is affected by the patient's demographics such as weight and height. Understanding the relationships between implant size and patients' demographics can provide useful information for new prosthesis design, implant test planning, and clinical data interpretation. Utilizing a manufacturer supported clinical database, this study examined the relationships between TKA patient's body weight, height, and body mass index (BMI) and the received implant size of a well-established implant system. Methods. A multi-site clinical database operated by Exactech, Inc. (Gainesville, FL, USA) was utilized for this study. The database contains patient information of Optetrak TKA implant recipients from over 30 physicians in US, UK, and Colombia since 1995. Nine implant sizes (0, 1, 2, 2.5, 3, 3.5, 4, 5 and 6) are seen in the database, while size 0 was excluded due to very low usage. Taking primary TKA only, a total of 2,713 cases were examined for patient's body weight, height, BMI, and their relationships with the implant size. Results. Both patient's weight and height strongly correlate with implant size (R. 2. »0.95 for both parameters with a linear regression). On average, the increase of one implant size corresponds to an increase of 7.4 kg in patient's weight and 7.0 cm in patient's height (Figure 1). However, there is almost no dependency between patient's BMI and implant size (R. 2. <0.05), and the regression line is almost flat (k=-0.08) (Figure 1). Discussion. Based on the Exactech database, this study revealed that TKA patients' weight and height increase close-to-linearly with implant size, but BMI stays fairly constant. These relationships are not all intuitive mathematically, and are likely simplified representations of higher order functions within the particular variable ranges. The most interesting finding was the independence of BMI on implant size, which provides a favorable validation of the geometry design and size selection of the Optetrak implant system. BMI (kg/m. 2. ) has the same unit dimension as stress (N/m. 2. ) excluding the constant g (9.8 N/kg). Since implant geometry is generally proportional to patient height, and joint force is generally proportional to patient weight, the mechanical stress imposed on the implant would be generally proportional to patient's BMI. The fact that BMI stays constant across sizes indicates that the implant system would experience a similar level of stress across all sizes, which has been previously observed in femorotibial contact stress analyses on the Optetrak system. This study showed that a heavier TKA patient statistically tends to receive a larger implant which, depending on implant design, will provide larger contact area and compensate for the higher load

Objective. This paper aims to analyze the kinetics of the over-ground wheel-type body weight supporting system (BWS); tendency changes of low extremity joint moment (hip, knee, ankle), 3 axis accelerations of a trunk, cadence and gait velocity as weight bearing level changes. Method. 15 subjects (11 males, 4 females, age:23.63.5, height:170.65.1cm, weight:69.0210.75kg) who had no history of surgery participated. 6 levels (0%, 10%, 20%, 30%, 40% and 50%) of BWS were given to subjects at self-selected gait velocity and kinetic data was calculated using a motion capture system, Vicon. ®. (Vicon, UK). Results. Maximum joint moments at the hip, knee, and ankle decrease as weight bearing increases on the sagittal plane. However, no significant decrease was found after 20% level of BWS at the hip and knee joint. On the other hand, the maximum ankle joint moment keeps decreasing. The root mean square (RMS) values of the acceleration in three directions: anterior-posterior (AP), medial-lateral (ML), and vertical(V) are analyzed. All 3-dimensional accelerations decrease as BWS increases while there is no significant difference over 20% level of BWS in the ML acceleration. V acceleration is reduced almost by half as soon as BWS level starts, but no further significant decrease can be found after 30% level of BWS. The AP acceleration tends to keep decreasing as BWS level increases. The cadence and gait velocity with wheel-type BWS decreases as BWS increases. Discussion. The maximum joint moments of the hip and knee do not significantly decrease when BWS exceeds a certain level, which is different from the case with BWS on treadmill; the maximum moments tend to keep decreasing linearly as BWS level increases on treadmill. In the case of the hip joint, the maximum moment is generated between toe-off and pre-swing phase, which generates force to push a trunk forward. With higher BWS, forward progression of the trunk is assisted by the wheel rather than driven by the lower extremity. It should be noticed that not only the tendency is different from BWS on treadmill, but the magnitude of the maximum hip moment is smaller than that of BWS on treadmill when BWS level is over 20%. The maximum knee joint moment is generated at the loading-response phase working as braking and shock absorption during gait, and thus the decrease in the maximum knee moment implies that less braking and shock absorption are required as BWS level increases. Only the maximum ankle joint torque keeps decreasing as BWS increases. The ankle moment is considered the largest contributor to forward acceleration. The tendency of the maximum ankle moment and the AP acceleration are similar (to what?) as weight bearing proceeds, which implies that walking speed slows down with the wheel-type BWS; the cadence is also reduced as BWS increases. Conclusion. The results highlight the difference of wheel-type BWS from BWS on treadmill, and provide information on how BWS level affects the joint moment and gait patterns. These outcomes can be utilized as a guideline of gait rehabilitation for people with lower-limb musculoskeletal impairments

Aim. Vancomycin is frequently used for bone and joint infections (BJI) because of the main role of Gram-positive bacteria as potential causal agents. It is crucial to achieve optimal vancomycin plasma concentrations since the first day to maximize treatment clinical and microbiological efficacy. The aim was to describe the patients’ profile that are more likely to achieve an optimal pharmacokinetic/pharmacodynamics (PK/PD) vancomycin target in the first therapeutic drug monitoring (TDM) sample. Methods. Retrospective study (March 2018-January 2022) in a university hospital including all patients treated with vancomycin for a BJI and undergoing TDM. Initial dose (1g/8-12h) was selected by the responsible clinician. Vancomycin plasma concentrations were obtained pre-dose (Cmin,ss) and 60-minutes after the infusion on day 2 of treatment. Global exposure measured by the area under the curve of plasma concentrations during 24h (AUC024h) was estimated using a bicompartmental PK model. An AUC024h/CMI=400–600mg*h/L was considered optimal, <400 infratherapeutic and >600 supratherapeutic, based on recent guidelines, and patients were classified into these 3 groups. A value of CMI=1 mg/L was considered, following guidelines recommendations. Categorial data: percentages and quantitative data as mean (standard deviation). Results. Ninety-five patients were included: 22(23.2%), 43(45.3%) and 30(31.6%) presented an infratherapeutic, optimal and supratherapeutic PKPD target, respectively. Medium age was 75,8(13,5) in the supratherapeutic group versus 57,2(16,3) in the infratherapeutic group. Weight (kg) was higher in the infratherapeutic group 80,8(18,4) versus 66,8(15,5) in the supratherapeutic group. Vancomycin dose (mg/kg/d) was 43,5(12,4) in the supratherapeutic group versus 34,5(10,8) in the infratherapeutic group. There were 17(56,7) patients who received 1g/8h of vancomycin in the supratherapeutic group and 6 (27,3) in the infratherapeutic group. Baseline glomerular filtration rate (BGF (CKD-EPI) (mL/min/1.73m2) was 71,5(20,1) in the supratherapeutic group and 100,0 (19,9) in the infratherapeutic group. The AUC24h/CMI was 788,0(186,1) in the supratherapeutic group and 323,7(55,4) in the infratherapeutic group. Significant differences observed in age, body weight (BW), baseline renal function and dose/frequency of vancomycin. Dosage adjustments recommendations were made in 62(65.3%) patients: 31(32.6%) dose-increase, 29(30.5%) reduction and 2 cases (2.1%) a temporary suspension. Conclusions. Less than 50% of patients achieved an optimal exposure of vancomycin on day 2 of treatment. Patients with infratherapeutic levels had a younger age and a higher body weight and glomerular filtration rate. In addition, they had received a lower vancomycin initial dose. On the contrary, a potentially toxic exposure was observed within older patients with impaired baseline renal function. These data suggest the relevance of an early vancomycin TDM for optimizing the treatment of BJI

Aim. The use of bone substitutes such as calcium sulfate (CaSO4) and hydroxyapatite with local antibiotics are crucial in the treatment of osteomyelitis. They allow the treatment of the dead space and locally provide large concentrations of antibiotics. However, it is unknown whether use of local vancomycin may elute and influence on vancomycin plasma levels. The aim of this study is to assess whether the addition of vancomycin to CaSO4 with hydroxyapatite may increase vancomycin plasma concentrations in in patients with osteomyelitis and therefore alter dosage adjustments. Method. The present study investigates the vancomycin plasma concentrations at 72–94 h post-surgery after the application of local vancomycin within CaSO4 (660mg vancomycin/10cc) and hydroxyapatite bone substitute in patients treated with empiric intravenous vancomycin and surgically treated for osteomyelitis. Vancomycin plasma concentrations were analyzed in twelve patients with osteomyelitis surgically treated with local release of vancomycin by CaSO4 and hydroxyapatite and undergoing therapeutic drug monitoring (TDM) of their vancomycin plasma concentrations as it is routinely done in our hospital. From 2019 to 2022, demographic data, microbiology, type of osteomyelitis, amount of local vancomycin applied, alteration of renal function, and vancomycin levels were retrospectively analyzed. Results. Twelve patients were included: 9(75%) were men. Median (range) demographic and clinical data: age: 51(26–67) years; body mass index: 27.7(18–46.4) kg/m2;baseline serum creatinine: 0.85 (0.7–1.24)mg/dl and 5(41.7%) with and glomerular filtration rate < 90ml/min(CPD-EPI, ml/min). Most frequently isolated microorganisms were Staphylococci (58%). Seven (54%) patients were classified as Cierny-Mader Osteomyelitis type III, 3(23%) as type IV and 2(23%) as type I. Treatment data: initial dose of vancomycin: 1g/8h in 9(75.0%) and 1g/12h in 3(25%) patients, total daily dose/body weight: 35.3(15.9–46.2) mg/kg. Pharmacokinetic data:days of iv vancomycin treatment until first TDM measurement: 3(3–4) days; minimum and maximum vancomycin plasma concentrations: 9.4(3–17.3) mg/L and 19.6(11.3–33.4) mg/L, respectively; patients with therapeutic concentrations: 6(50%); infratherapeutic: 4(33.3%) and supratherapeutic/potentially toxic: 2(16.7%). These 2 patients were young, had a baseline conserved renal function and were receiving the higher dose of 1g/8h. Conclusions. Vancomycin incorporated into the bone substitute appears not to increase blood concentrations of the glycopeptide in patients with osteomyelitis treated surgically and with intravenous vancomycin. However, 2 of the 12 patients presented supratherapeutic and potentially nephrotoxic vancomycin concentrations in the first TDM measurement, even though they were young and without renal impairment and needed and unexpected dose reduction. These results suggest the need to confirm the safety of local vancomycin in further larger clinical studies

Introduction. When evaluating the biomechanical performance of a total knee arthroplasty (TKA) implant design, device companies are usually required to select the “worst case scenario” for testing by the regulatory bodies. However, most test standards (e.g., ASTM, ISO) do not explicitly specify how the “worst case” should be determined. It is quite often that an extreme size (the smallest or the largest) in a system is taken as the “worst case” size. The smallest size is sometimes selected under the rationale that it has the smallest geometry thus the weakest mechanical structure. While the largest size is sometimes selected under the rationale that it is used on the biggest patients associated with the highest loads. However, implant geometry and in vivo load are two compounding factors that together determine the implant's biomechanical challenge. As the result, the true “worst case” must be determined considering both factors, and the choice could be design-specific. This study evaluated the femorotibial contact stress of a TKA implant system, and demonstrated that the extreme sizes may not simply be the “worst case”. Methods. The femorotibial contact stress of a posterior-stabilizing TKA implant system was assessed using finite element analysis. Multiple sizes ranging from size 0 to 6 were analyzed. For each size, the CAD models were assembled at knee extension. A load equivalent to 4 times of patient body weight was applied. Average patient body weights were calculated based on the company's clinical database: 72.5, 76.0, 80.0, 87.4, 95.2, 103.4, and 111.0 kg for sizes 0, 1, 2, 3, 4, 5 and 6, respectively. Von Mises stresses in the polyethylene tibial insert were examined and compared among different sizes. Results. The peak femorotibial contact stress was found to be 20.0, 19.4, 19.2, 20.6, 20.4, 18.9 and 20.0 MPa for sizes 0, 1, 2, 3, 4, 5 and 6, respectively. The difference between the highest (size 3) and the lowest (size 5) was less than 9%. Neither size 0 nor size 6 represented the “worst case” in the scope. Discussion. Due to the cross-influence of two compounding factors (geometry and load), the determination of the “worst case” in an implant system is not as simple as how the question is often handled. For the implant system analyzed in this study, from the smallest to the largest size, the dimension of the tibial insert grew by 49% while the average patient body weight also grew by about 53%. Under the influencing of both factors, the outcome contact stress showed little variation across sizes. Neither the smallest nor the largest size demonstrated the “worst case”. It should be noted that the finding in this study may not directly apply to other TKA implant systems of different designs. The implant system analyzed in this study features a matched femorotibial geometry on every size, which is able to produce a “proportional” mechanical response. This study highlighted the importance of a more thorough assessment when selecting the clinical worst case for implant testing

Introduction. In a previous study of subjects with no history of lower extremity injury or disease we found a linear relationship between body weight and peak hip, knee, and ankle joint forces during the stance phase of gait. To investigate the effect of total knee arthroplasty (TKA) on forces in the operated joints as well as the other joints of the lower extremities, we tested TKA subjects during gait and performed inverse dynamics analyses of the results. Materials and Methods. TKA subjects (3 M, 1 F; 58 ± 5 years; body mass index range (BMI): 26–36 kg/m. 2. ) participated in this investigation following institutional review board approval and informed consent. One subject had bilateral knee replacement. Each patient received the same implant design (4 PS, 1 CR). Data from previously tested control subjects (8 M, 4 F; 26 ± 4 years; BMI: 20–36 kg/m. 2. ) were used for comparison. Retro-reflective markers were placed over bony landmarks of each subject. A nine-camera video-based opto-electronic system was used for 3D motion capture as subjects walked barefoot at a self-selected speed on a 10 meter walkway instrumented with three force plates. Data were imported into a 12-body segment multibody dynamics model (AnyBody Technology) to calculate joint forces. Each leg contained 56 muscles whose mechanical effect was modeled by 159 simple muscle slips, each consisting of a contractile element. The models were scaled to match each subject's anthropometry and BMI. For the control subjects, only one limb was used in determining the relationship between body mass and peak joint force at the hip, knee, and ankle. For the TKA subjects, the peak joint forces were calculated for both the TKA limb and the contralateral limb. Results. Figure 1 shows the knee joint forces for the TKA subjects’ operated (red triangles) and contralateral knees (diamonds) along with the values for the control subjects (circles). Knee joint forces for the TKA subjects fell within or near the upper and lower 95% confidence intervals (dashed lines) of the mean regression lines (solid lines) for the control subjects. Three patients had other lower limb complications (osteoarthritis, ankle surgery). One subject favored the operated limb and another the non-operated limb, as ascertained from the corresponding hip (Figure 2) and ankle joint forces (Figure 3). Discussion. Modeling and simulation can be used to indirectly estimate joint forces in the implanted and non-operated joints. Our gait-lab derived inverse dynamics simulations suggest that joint forces following TKA fall within or near the normal range over a wide range of body weights and that the linear dependence between joint force and body weight applies to the implanted as well as non-implanted joints

Introduction. Femoral shaft fractures in children is a serious injury that needs hospitalization, with a high prevalence in the age group 6–8 years old. Various treatment options are available and with a comparable weight of evidence. Submuscular plating provides a dependable solution, especially in length-unstable fractures and heavier kids. We present a novel technique to facilitate and control the reduction intraoperatively, which would allow for easier submuscular plate application. Materials and Methods. We have retrospectively reviewed four boys and three girls; all were operated in one centre. Polyaxial clamps and rods were applied to the sagittally-oriented bone screws, the reduction was done manually, and the clamps were tightened after achieving the proper alignment in the anteroposterior and lateral fluoroscopy views. The submuscular plate was applied as described, then clamps and bone screws were removed. Results. The mean age at surgery was 13 years (range, 9–14). The mean body weight was 43.3 kg (range, 30–66). There were five mid-shaft fractures, one proximal third and one distal third. There were Four type A fractures, two type B and one type C. Four patients had road traffic accidents while three had direct trauma. The mean preoperative haemoglobin concentration 12.5 g/dl (range 11.3–13 g/dl). No blood transfusion was needed intraoperatively or postoperatively. The operative time averaged 122 minutes, and the mean hospital stay was one (range 1–4 days). The patients reported no pain at a mean of 1.5 weeks (range, one-three weeks). All fractures united at a mean of 8.7 weeks (range 6–12 weeks). No wound healing problems nor deep infections happened. The knee joint range of motion was full in all patients at six weeks postoperatively. There was no mechanical irritation from the inserted plate. At the final follow-up, all fractures united without malalignment nor length discrepancy. Conclusions. External fixator-assisted internal fixation of pediatric femoral fractures would facilitate the accuracy and control of fracture reduction and allow minimally invasive percutaneous osteosynthesis. Our study has shown a decrease in operative time, and an accompanying reduction in length of inpatient stay, prolonged need for analgesia and post-operative rehabilitation

INTRODUCTION:. Clinical densitometry studies indicate that following TKR implantation there is loss of bone mineral density in regions around the implant. Bone density below the tibial tray has been reported to decrease 36% at eight years after TKR. This bone loss (∼5%/year) is substantially greater than osteoporosis patients in the same age group (∼1–2%/year) and could contribute the loss of mechanical support provided by the peri-implant leading to loosening of components in the long term. High patient mass and body mass index have also been implicated in increased loosening rates, and was thought to be due to high stress or strain on the tibial constructs. These findings suggest that peri-implant bone strain may be affected by time in service and patient factors such as body mass. The goal of this project was to assess the proximal tibial bone strain with biomechanical loading using en bloc retrieved TKR tibial components. Note that the implants were not obtained from revision surgery for a loose implant, but rather after death; thus the implants can be considered to be successful for the lifetime of the patient. We asked two research questions, guided by the clinical and laboratory observations: (1) are the peri-implant bone strain magnitudes for cemented tibial components greater for implants with more time in service and from older donors?, (2) is tibial bone strain greater for constructs from donors with high body weight and lower peri-implant BMD?. METHODS:. Twenty-one human knees with cemented total knee replacements were obtained from the SUNY Upstate Medical University Anatomical Gift Program. Clinical bone density scans were obtained of the proximal tibia in the anterior-posterior direction. Axial loads (1 body weight, 60/40% medial to lateral) were applied to the tibia through the contact patches identified on the polyethylene inserts. Strain measures were made using a non-contacting 3-D digital image correlation (DIC) system. Strain was measured over six regions of the bone surface (anterior (A), posterior (P), medial (M), lateral (L), postero-medial (PM), postero-lateral (PL)) (Figure 1). RESULTS:. For a donor population of 54 to 90 years (78 ave) with 0 to 22 years in service (ave 9 years), the peri-implant bone strains ranged from 119 to 791 ue. Maximum strains exceeded 3000 ue. Peri-implant bone strains were greater for implants with more time in service (p = 0.044), but not age of the donor (p = 0.333) (Figure 2). Peri-implant bone strains were greater for donors with greater mass (p = 0.028) and lower bone density (p = 0.0039) (Figure 3). DISCUSSION:. To the authors knowledge, these results show for the first time (using cemented tibial components) that bone remodeling after in-vivo service does not result in constant bone strain as would be expected for ‘homeostatic’ strain conditions. Even though loading was applied based on body weight, heavier donors had higher bone strains. Donors with more time in service also had higher bone strains. Combined, these results suggest that the supporting bone stock could diminish in some patients to the point at which bone failure occurs resulting in component migration

INTRODUCTION. The increasing incidence of periprosthetic femoral fractures (PFF) after total hip arthroplasty presents growing concerns due to challenges in treatment and increased mortality. PFF are often observed when the prosthesis is implanted in varus, especially with blade-type stems. To help elucidate its impact on the PFF risk, the specific research question is: What is the effect of misalignment of a blade-type stem (resulting in down-sized prosthesis) on 1)the distribution and magnitude of cortical stresses and 2)implant-bone micromotion. METHOD. We developed two finite element models consisting of an average female femur implanted within a generic blade-type stem prosthesis, (i)in neutral alignment, and (ii)oriented in 5° of varus, coupled with corresponding down-sizing of the prosthesis. Each model consisted of 1.1million elements, while the average mesh length at the implant-bone interface was 0.4mm. Elastic moduli of 15GPa(cortex), 150MPa(trabecular bone), and 121GPa(implant), and Poisson's ratio of 0.3 were assumed. The distal end was fixed and the interface was defined as a surface-to-surface contact with friction coefficients (dynamic 0.3; static 0.4). Walking and stair-climbing were simulated by loading the joint contact and muscle forces after scaling to the subjects’ body weight. The peak von Mises stress and the average stress within the surface having 1cm diameter and the center at where the peak stress occurred at each contacting area, the interfacial micromotion along medial, lateral side were analyzed. For statistical analysis, two-tailed t-test was performed between the neutral and varus cases over four loading cycles with significance level of p<0.05. RESULTS. Neutral alignment led to three areas of cortical/implant contact with focal load transfer via those areas, whereas varus placement limited to two areas (Figure 1). In both simulations, the greatest stress was observed at the proximal medial contact. With varus, average and peak stresses increased by 39% and 65% during walking and 28% and 35% during stair-climbing, respectively (Table 1). Micromotion was greatest over the proximal third of the interface, especially along lateral side (Figure 2). The 90. th. percentile values with the varus exceeded the neutral by 35% with walking and 28% with stair-climbing over the lateral interface. DISCUSSION. The proximal medial location of the greatest stress correlates well with clinical observations in PFF involving a posteromedial calcar fragment. Based on current lesser stress than the reported yield stress, loading during daily living activities may result in microdamage rather than an immediate PFF. However, impact loading such as hammering for stem insertion may introduce PFF at the location, especially with in varus. The increase in interfacial micromotion is expected to lead to increase in the risk for implant loosening, also leading to PFF. Further study is needed to confirm the validity and generalizability of these findings. SIGNIFICANCE/CLINICAL RELEVANCE. This study demonstrates the importance of proper alignment of femoral stems of a blade-type design. The misalignment (resulting in down-sizing) increased stress up to 65% and micromotion up to 35% around prosthesis, even during daily activities, thus increased attention to proper implant alignment and sizing is suggested when using components of this design. For any figures or tables, please contact the authors directly

To determine the effect of Dexamethasone on post-operative pain management in patients undergoing Total Knee Arthroplasty in terms of numerical pain rating scale and total opoid consumption. This Randomized Controlled Trail (RCT) was conducted for 02 years (7th September 2015 to 6th September 2017). All patients undergoing primary Unilateral Total Knee Replacement (TKR) for Osteoarthritis knee were included in the study. Patients with poor glycemic control (HbA1c > 7.6), Hepatic/Renal failure, corticosteroids/ Immunosuppression drug usage in the last 06 months, known psychiatric illnesses were excluded from the study. All patients were operated by consultant Orthopaedic surgeon under Spinal Anaesthesia and tourniquet control using medial para-patellar approach. Patients were randomly divided into 02 groups, A and B. 79 patients were placed in each group. Group A given 0.1mg/kg body weight Dexamethasone Intravenously 15 minutes prior to surgery and another dose 24 hours post-operatively while in group B (control group) no Dexamethasone given. Post-operative pain using the numerical pain rating scale (NRS) and total narcotics consumed converted to morphine dose equivalent noted immediately post-op, 12-, 24- and 48-hours post-operatively. Data analysis done using SPSS version 23. A total of 158 patients were included in the study. Of the total, 98 (62.02%) were females and 60 (37.98%) males. Average BMI of patients 26.94 ±3.14 kg/m2. Patients in group A required less post-operative analgesics (p < 0 .01) and had a better numerical pain rating scale score (p < 0 .01) as compared to group B. Pain scores at 24- and 48-hours post-op were significantly less for Dexamethasone group (p < 0 .01). Use of Dexamethasone per- and post-operatively reduces the pain and amount of analgesics used in patients undergoing TKA. For any reader queries, please contact . drjunaidrmc@gmail.com

There is high morbidity and mortality associated with infection following orthopaedic procedures. In accordance to local guidelines, most hospitals follow a set protocol for surgical prophylaxis, which expects a compliance rate of 100%. A new protocol was introduced to the orthopaedic department of a teaching hospital in August 2013, changing from a cephalosporin, with potential C. difficile risk, to teicoplanin and gentamicin, within 30 minutes of incision. Our aim was to audit how well the protocol was followed across 3 different time periods. Data was collected for 3 different time periods following the introduction of the new protocol (August-November 2013, April-May 2014 & November 2014) on the choice of antibiotic. Both elective and trauma cases were included. After each cycle, the data was presented to the orthopaedic surgical and anaesthetic departments to raise awareness and draw attention to the antibiotic prophylaxis posters in theatre. The 1st audit cycle (n=30) indicated that there was 0% compliance with the current protocol and 100% compliance with the previous protocol. The 2nd audit cycle (n=27) indicated that 0% complied with the current protocol, 54% complied with the previous protocol and that there was a combination of both protocols being used in 46% of the patients. Finally the 3rd audit cycle (n=33) indicated a 100% compliance rate in terms of antibiotic choice. However, only 9% were given the appropriate dose according to body weight and within the appropriate time based on the documented evidence. This audit demonstrates the value of auditing and then disseminating the findings to relevant departments to influence practice. Each audit cycle demonstrated a progressive uptake in compliance with the hospital trust's antibiotic prophylaxis policy. The last audit cycle highlighted discrepancy in dosage based on weights; a further intervention will be to provide ideal body weight (IBW) vs dose tables in all orthopaedic theatres to ensure the correct antibiotic dosage is given

Introduction. The popliteus tendon is a component of the posterolateral corner of the knee, which controls the external rotation of the tibia. In our clinical practice, the femoral footprint of the popliteus tendon is occasionally excised as the bone is resected during total knee arthroplasty (TKA). Although the excision of the popliteus tendon femoral footprint could result in excessive external rotation of the tibia and may have adverse effects on the long-term outcomes of TKA, little attention has been paid to the popliteus tendon femoral footprint during TKA. The purpose of the present study is to assess the frequency of the excision and its associated risk factors. Methods. One hundred eleven knees of 90 patients with varus knee osteoarthritis who underwent primary TKA were included in the present study. There were 13 males and 77 females, and their average age was 74 years. The NexGen knee replacement system (Zimmer, Warsaw, IN, USA) was used in all cases. The excision of the popliteus tendon femoral footprint was intraoperatively evaluated, and the patients were divided into three groups depending on the status of the femoral footprint, i.e., the preserved, partially excised, and completely excised groups. The thickness of the distal femoral osteotomy, femoral component size, and background data including height, body weight, gender, and age were compared among these groups. Analysis of variance followed by Student–Newman–Keuls test were used to compare the continuous values and ordinal scales. Gender was compared using Fisher's exact test and residual analysis. Statistical significance was set at p < 0.05. Results. The popliteus tendon femoral footprint was preserved in 48 knees (43.2%), partially excised in 45 knees (40.5%), and completely excised in 18 knees (16.2%). The mean patient height was 154.6, 150.1, and 148.7 cm in the preserved, partially excised, and completely excised groups, respectively, and these differences were statistically significant (p < 0.01). Femoral component size was significantly smaller in the partially and completely excised groups compared with that in the preserved group (p < 0.05). The preserved group included more male patients (p < 0.01). There were no significant differences in body weight, age, and thickness of the distal femoral osteotomy among the groups. Conclusion. The partial or complete excision of the popliteus tendon femoral footprint was observed in more than half of the evaluated knees. Shorter height, smaller femoral component size, and female sex were considered to be the possible risk factors for the excision of the popliteus tendon femoral footprint

One of the main concerns about the currently available simulators is that the TKA is driven in a “passive way” for assessment. For the simulators for the wear assessment, the tibio-femoral relative motion is automatically made by using the knee kinematics and loading profile of a normal gait. As for the simulators for the kinematics and kinetics assessment of TKA, also the predicted loading profiles introduced from the theoretical model are applied as the input data to drive the simulator. It should be noted that the human joints are driven by the muscles' forces and external loads, and their kinematics and kinetics are the “outcome”. This being so, the knee simulator should be driven by the muscles' forces and upon these conditions the TKA performance is to be assessed. Some other concerns about the current simulations are as follows. The effects of hip joint motion are not taken into account. The upper body weight is applied along a vertical rod in such a way as a crank-slider. Furthermore, few simulators are capable of knee flexion greater than about 110°. Considering the above, we have developed a novel knee simulator which makes it possible to reproduce the active and natural knee motion to assess kinematics and kinetics of TKA. In the experiment, the custom-designed PS type TKA was attached and the simulator was operated so as to reproduce the sit-to-stand features, thereby introducing the tibio-femoral loading profiles during the motion. Figure 1 illustrates the external appearances of the simulator and a close view of the knee joint compartment. Since our simulator is composed of a multiple inverted pendulum, the knee part bears the upper body weight in a physiological way. The holder bracket is set to prevent the simulator from collapsing for security. The dimension and weight of each link were set as close as those of each segment of a normal male subject. Our simulator is driven by the wire pull mechanism which substitutes the human musculo-skeletal system of lower limb. Figure 2 shows close views of tibial tray with load cells. In Fig.2a, cell FR, FC and FL are to measure the tangential components of tibio-femoral contact force, i.e., the Anterio-Posterior force (AP force). The rest five cells are to measure the normal components of tibio-femoral contact force (normal force). As shown in Fig.2c, the tibial insert of TKA is mounted on the lid of the tibial tray box. In the experiment, a PS type TKA whose maximum flexion angle of 150° was attached to the simulator for evaluation. The simulator was operated so as to reproduce the sit-to-stand features and the data concerning about the AP force, Ft, and the normal force, Fn were recorded. Figure 3 shows the variations of knee flexion angles and knee contact forces respectively as a function of normalized time. Our knee simulator may have a potential for substituting the in vivo measurement

Introduction. In THA of DDH cases, sometimes shortening and/or derotational subtrochanteric osteotomy is required, for cases with high hip center and/or high anteversion. Initial fixation is one of the most important problems after subtrochanteric osteotomy. To prevent rotational displacement V-osteotomy or step osteotomy is often used. Even though until the osteotomy part unites, additional fixation is required. When a stem with distal load transfer was used body weight can be transferred to healthy part, so early full weight bearing should be expected. However, the muscles around hip joint can pull up proximal part, so it would be possible osteotomy part to be split. When a stem with proximal load transfer, body weight would be loaded on non united osteotomy part. So full weight bearing could sometimes be postponed. A stem that has both proximal and distal load transfer, and has facility for prevent rotation, those situations would possibly be simply solved. Lima (Italy) has a proximal load transfer conical stem with fins “Modulus” and a distal load transfer conical stem “Revision.” Combining these two stems, a stem as explained prior was designed. In the present study, applicability of the stem for cases such as subtrochanteric osteotomy was assessed. Materials and Methods. The stem geometry data were provided by the maker. Forty CAT scan DICOM data, 12 male, 28 female, 58+/−13.8 Y.O. were transferred to STL geometry data using Mimics®. Then using Magics® fit studies were done. For each femur, most suitable size of conventional “Modulus” and double conical stem “Modulus R” were selected to have tight fit making greater trochanter top height as head center height, then the area where stem core attaches to the inside surface of the canal were determined. Results. Three cases were excluded, as they are very small and could not find small enough stems. With the rest, 37 cases “Modulus R” could obtain the same proximal contact area and in average 26.9% more area in distal area. (Fig.1). Discussion. Double conical stem could have been expected to useful for the cases subtrochanteric osteotomies. In the actual case with 42 mm higher hip center, final elongation was determined as 25 mm. Then 17mm shortening subtrochanteric osteotomy was designed. (Fig. 2) Very tight fixation including rotational stability was obtained during the surgery. The patient could stand up since the next day. Full weight bearing was obtained in one week. Good bone formation was obtained in 2M. (Fig.3)

Introduction. Our primary hypothesis was simple: does gait on a downhill gradient distinguish between types of knee arthroplasty? Our secondary hypotheses were these: are stride length and other kinematic variables affected by cruciate ligament integrity following knee arthroplasty?. Participants. Ethical approval was sought and gained prior to commencement of the study. 52 subjects were tested on the instrumented treadmill, 3 groups (UKA, TKA, and young healthy control) of 19, 14, and 19 respectively. The two high performing arthroplasty groups were recruited from a database of patient related outcome measures (PROMs) and were chosen based on high Oxford knee scores (OKS) with a minimum 12 months post hip arthroplasty. Gait Analysis. Gait performance was tested on a validated instrumented treadmill (Kistler Gaitway®, Kistler Instrument Corporation, Amherst NY)[22, 23]. The rear of the treadmill was ramped with 30 cm axle stands in order to create a 7 degree decline for downhill walking (figure 1). The speed was increased incrementally. Hof scaling and body weight normalising was also applied to the outputted mechanical data to correct for leg length and mass differences, respectively. Results. Patient Related Outcome Measures. Both arthroplasty groups outcome scores were substantially better than the average reported by national joint registries. Treadmill Gait Analysis. When walking fast downhill, UKA patients walked 15% faster than the TKA patients (1.75 vs 1.52 m/sec p=0.000) despite having the same cadence (134 vs 135step/min) (figures 2,3,4). The 15% difference in speed was largely due to the reduced mean step (p=0.001) and stride lengths (p=0.000) seen in the TKA patients. These finding persisted after Hof scaling, which normalised speed for leg length (p=0.000). The values are indicated as means ± standard deviation; †significant difference between implant versus control (p <0.05); ‡significant difference between implant groups (p<0.05);H=normalized to leg length; BW=normalized to body weight. Discussion. The UKA group walked 15% faster than the TKA, with stride length almost matching the normal controls. The presence of intact cruciate ligaments allow a normal and co-ordinated swing phase, enabling the more normal stride, while the absence of the anterior cruciate ligament contributes to the reduction of knee flexion in swing phase, and thus the shorter stride length

Introduction. Ankle arthrodesis is a common treatment for destroyed ankle arthrosis with sacrificing the range of motion. On the other hand, total ankle arthroplasty (TAA) is an operation that should develop as a method keeping or improving range of motion (ROM); however, loosening and sinking of the implant have been reported in especially constrained designs of the implant. The concept of FINE TAA is the mobile bearing system (Nakashima Medical Co., Ltd, Okayama Japan) that can reduce stress concentration to implants. The purpose of this study is to evaluate the short-term results of FINE TAA. Objectives and Methods. We performed FINE TAA for osteoarthritis (OA) (2 ankles of 2 patients) and rheumatoid arthritis (RA) (4 ankles of 3 patients). All patients were female. The mean age of the patients was 71.4 years old at the operation. The mean follow-up period was 32.6 (range, 18–55) months. All patients were assessed for Japan Orthopedic Association (JOA) score and ROM in plantar flexion and dorsiflexion at the point of pre-operation and final follow-up. We evaluated radiolucent line, subsidence, and alignment of implants at the latest follow-up. Results. JOA score improved from 34.8 to 72.2 on average. ROM improved from 4.0 ± 5.5 º to 7.0 ± 4.5 º on average in plantar flexion and from 21.0 ± 17.0 º to 31.0 ± 16.0 º in dorsiflexion. One case underwent an ankle arthrodesis because of the implant loosening. This failed case was very obese (70 kg of body weight, 31.0 of Body Mass Index) and her activity was relatively high. One ankle showed radiolucent line around the components with no symptoms. The alignment of implants was slightly varus and anteversion (the mean values of alpha angle was 88.0 ± 1.2º, beta angle was 84.0 ± 9.2º, and gamma angle was 2.1 ± 0.2º). Discussion. The ankle joint is highly loaded up to five times body weight on small surface of contact area during walking. Therefore, the poor results have been published after TAA with using fixed-bearing 2-component prostheses compared to ankle arthrodesis. On the other hand, FINE TAA was designed as 3-component mobile bearing system that can reduce stress concentration compared to conventional TAA. We experienced implant failure in one obese case but short-term results of other cases were acceptable. Good clinical results can be expected with FINE TAA except for the obese case. We should pay careful attention to the surgical indication. Conclusion. Our short term results of FINE TAA were acceptable except for one obese case. We should evaluate further mid- and long- clinical results

When a knee flex deeply, the posterior side of thigh and calf contact. The contact force is unignorable to estimate the load acting on a knee because the force generates extensional moment on the knee, and the moment might be about 20–80% of the flexional moment generated by a floor reacting force. Besides, the thigh-calf contact force varies so much even if the posture or the test subject are the same that it is hard to use the average value to estimate the knee load. We have assumed that the force might change not only by the individual physical size but also by a slight change of the posture, especially the angle of the upper body. Therefore we tried to create the estimation equation for the thigh-calf contact force using both anthropometric sizes and posture angles as parameters. The objective posture was kneeling, both plantarflexing and dorsiflexing the ankle joint. Test subjects were 10 healthy males. They were asked to sit on a floor with kneeling, and to tilt their upper body forward and backward. The estimation equations were created as the linear combinations of the parameters, determining the coefficient as to minimize the root mean square errors. We used the parameters as explanatory variables which could be divided into posture parameters and individual parameters. Posture parameters included the angle of upper body, thigh and lower thigh. Individual parameters included height, weight, axial and circumferential lengths of thigh and lower thigh. The magnitude of the force was normalized by a body weight, and the acting position was expressed by the moment arm length around a knee joint and normalized by a height. As a result, the adjusted coefficient of determination improved and the root mean square error decreased when using both posture and individual parameters, though there were large errors when neglecting either parameters. The accuracy decreased little when using the same equation for plantarflexed and dorsiflexed kneeling in magnitude. The relation of measured and estimated values of the magnitude and acting position, using the common equation with all the parameters. It might be because the difference of the postures could be described by the inclination angle of a thigh. In both postures, the magnitude of a thigh-calf contact force was mainly affected by the posture and acting position by the individual parameters. When calculating the knee joint load, the errors would be about 8.59 Nm on the knee moment and 290 N on the knee load when using just an average, and they would decrease to 2.23 Nm and 74 N respectively using the estimation equation

Background. We would like to analyze the risk factors of no thumb test among knee alignment tests during total knee arthroplasty surgery. Methods. The 156 cases of total knee arthroplasty by an operator from October 2009 to April 2010 were analyzed according to preoperative indicators including body weight, height, degree of varus deformity, and patella subluxation and surgical indicators such as pre-osteotomy patella thickness, degree of patella degeneration, no thumb test which was evaluated after medial prepatella incision and before bone resection (1st test), no thumb test which was evaluated with corrective valgus stress (2nd test, J test), and the kind of prosthesis. We comparatively analyzed indicators affecting no thumb test (3rd test). Results. There was no relation between age, sex, and body weight and no thumb test (3rd test). Patellar sulcus angle (p = 0.795), patellar congruence angle (p = 0.276) and preoperative mechanical axis showed no relationship. The 1st no thumb test (p = 0.007) and 2nd test (p = 0.002) showed signifi cant relation with the 3rd no thumb test. Among surgical indicators, pre-osteotomy patella thickness (p = 0.275) and degeneration of patella (p = 0.320) were not relevant but post-osteotomy patellar thickness (p = 0.002) was relevant to no thumb test (3rd test). According to prosthesis, there was no signifi cance with Nexgen (p = 0.575). However, there was signifi cant correlation between Scorpio (p = 0.011), Vanguard (p = 0.049) and no thumb test (3rd test). Especially, Scorpio had a tendency to dislocate the patella, but Vanguard to stabilize the patella. Conclusions. No thumb test (3rd test) is correlated positively with 1st test, 2nd test, and post-osteotomy patella thickness. Therefore, the more patella osteotomy and the prosthesis with high affi nity to patellofemoral alignment would be required for correct patella alignment

Background. Total ankle arthroplasty (TAA) is an alternative to ankle arthrodesis, replacing the degenerated joint with a mechanical motion-preserving alternative. Implant loosening remains a primary cause of TAA revision, and has been associated with wear-mediated osteolysis. Differing implant designs have a major influence on the wear performance of joint replacements. Providing a range of implant sizes allows surgeons a greater intra-operative choice for varying patient anatomy and potential to minimise wear. Minimal pre-clinical testing exists in the literature that investigates the effect of implant size on the wear behaviour. The aim of this study therefore was to investigate the effect of two different implant sizes on the wear performance of a TAA. Materials & Methods. Six ‘medium’ and six ‘extra small’ BOX® (MatOrtho Ltd, UK) TAA implants, of the same conceptual design and polyethylene insert thickness, were tested in a modified 6 station pneumatic knee simulator. 5 million cycles (Mc) of wear simulation were completed for each implant size, under kinematics aiming to replicate an ankle gait cycle (Figure 1) [1]. The simulator used had six degrees of freedom, of which four were controlled. The maximum axial load was 3150N, equivalent to 4.5 times body weight of a 70kg individual. The flexion profile ranged from −15° plantarflexion to 15° dorsiflexion. Rotation about the tibial component ranged from −2.3° of internal rotation to 8° external rotation, and anterior/posterior (AP) displacement ranged from 3.1 mm anterior to −0.9 mm posterior displacement. The lubricant used was 25% bovine serum supplemented with 0.04% sodium azide to prevent bacterial degradation. The wear of the TAA polyethylene inserts were determined gravimetrically after each Mc, with unloaded soak controls used to compensate for the uptake of moisture by the polyethylene. Results. There were no significant differences (P = 0.872) in the mean wear rates (± 95% confidence limits) between the medium (11.00 ± 3.06 mm3/Mc) and extra small (10.64 ± 4.61 mm3/Mc) implant sizes (Figure 2). An observation of insert surfaces showed clear signs of abrasive wear and burnishing (Figure 3). There was evidence of polyethylene transfer and scratching on the tibial components, while talar components displayed fine linear scratching in similar directions for both implant sizes. Conclusions. The wear rates of both implant sizes are comparable to the wear rate (13.30 ± 2.50 mm3/Mc) of a previous wear study, which was conducted on ‘medium-sized’ Corin Zenith TAAs, under the same simulator conditions for 2 Mc [1]. The wear rates for both implant sizes are substantially lower than the wear of four ‘small-sized’ BOX® ankles (18.60 ± 12.80 mm3/Mc) for 2Mc [2]. The considerable difference in wear rates may be due to the lower forces, higher AP and deionised water as the test lubricant [2], which does not replicate the features of the natural synovial fluid and produce tribological artefact. The results from this study suggest that under the same kinematic and kinetic conditions, the wear rates are unaffected by a change in TAA implant size

There are several concerns about the current simulators for TKA. First, the knee is flexed in a “passive way” under the condition of applying constant muscular tension forces. Second, the effects of hip joint motion are not taken into account. Thirdly, the external load for example, upper body weight is not applied in a natural way. Finally, few simulators are capable of knee flexion greater than about 100°. To this end, we have developed a novel knee simulator system that reproduces the active and natural knee motion to evaluate kinematics and joint forces of TKA. Our simulator system has the following advantages and innovative features. First, it is driven directly by muscles' tension forces, and the knee is capable of active flexion. Secondly, a hip joint is incorporated into it and the lower limb motion is achieved in a synergistic way between the hip and knee joints. Thirdly, it is capable of complete deep knee flexion up to 180°. Figure 1 shows the structure of the system. Both the hip and knee joints are moved by the tension forces of four wires that simulate the functions of the mono-articular muscles ((1), (3)) and the bi-articular muscles ((2), (4)) by means of a multiple pulley system (Fig 2). The femoral and tibial components of TKA are secured in the distal end of the upper link (thigh) and the proximal end of the lower link (shank) respectively. The ankle assembly has three sets of rotary bearings whose axes intersect at a fixed point, the center of the ankle, allowing spherical movement of the tibia about the ankle center. Springs were stretched around the ankle center to substitute the muscles around the ankle. Weights I and II are counterweights so as to duplicate the weights of the human upper body, thigh and shank respectively. The wires are pulled to produce the hip and knee motions. The linear bearings running along vertical rods also prevent the system from collapsing. In the experiment, a custom-designed posterior stabilized type TKA was attached to the simulator system for evaluation. The system was operated so as to reproduce the sit-to-stand features in a quasi-static manner in order to study the kinematics of TKA. Beyond 130°, the knee proceeded to flex passively because of upper body weight. Conspicuous internal/external rotation or valgus/varus motion of the tibia relative to the femur was not observed as the knee flexed. When our simulator system was driven in a quasi-static manner, it was able to measure the kinematics of TKA however, when the system was driven in a dynamic manner, it oscillated because the springs around the ankle were not stiff enough to hold the inverted pendulum-like system upright and the ratios of the tension force exerted by the four wires simulating muscles could not be determined appropriately