Introduction

Lower limb open fractures are severe injuries, with a joint orthoplastic approach for management recommended by BOAST. An initial audit highlighted a discrepancy in time to definitive wound coverage between the Queen Elizabeth University Hospital (QEUH), which at the time was not an orthoplastic centre, and the Glasgow Royal Infirmary (GRI) which was. Our aim was to perform a secondary audit to identify if the introduction of an orthoplastic service at the QEUH led to a reduction in time to definitive wound coverage.

Aims

With increasing burden of revision hip arthroplasty (THA), one of the major challenges is the management of proximal femoral bone loss associated with previous multiple surgeries. Proximal femoral arthroplasty (PFA) has already been popularized for tumour surgeries. Our aim was to describe the outcome of using PFA in these demanding non-neoplastic cases.

With increasing burden of revision hip arthroplasty, one of the major challenge is the management of bone loss associated with previous multiple surgeries. Proximal femoral replacement (PFR) has already been popularised for tumour surgeries. The inherent advantages of PFR over allograft –prosthesis system, which is the other option for addressing severe bone loss include, early weight bearing and avoidance of non-union and disease transmission. Our study explores PFR as a possible solution for the management of complex hip revisions. Thirty consecutive hips (29 patients) that underwent PFR between January 2009 and December 2015 were reviewed retrospectively for their clinical and radiological outcomes. The Stanmore METS system was used in all these patients.

Mean age at the index surgery (PFR) was 72.69 years (range 50–89) with number of previous hip arthroplasties ranging from 1–5. At mean follow up of 32.27 months, there were no peri-prosthetic fractures and no mechanical failure of the implants. Clearance of infection was achieved in 80% of cases. There was 1 early failure due to intra-operative perforation of femoral canal needing further revision and two were revised for deep infection. Instability was noted in 26.7% (8) of the hips, of which, 87.5% (7) needed further revision with constrained sockets. Out of these 8 hips with instability, 5 had pre-operative infection. Deep infection was noted in 20% (6) of the hips, of which, 5 were primarily revised with PFR for septic loosening. However, further surgeries were essential for only 3 patients. One patient has symptomatic aseptic acetabular loosening and 1 had asymptomatic progressive femoral side loosening (lost to follow up).

Severe proximal femoral bone loss in complex revision arthroplasties has necessitated the use of PFR prosthesis. Our study supports the fact that PFR is probably a mechanically viable option for complex revisions. Significant numbers of dislocations and infections could be attributed to the poor soft tissue envelope around the hip. Further surgical techniques in the form use of dual mobility cups and silver coated PFR implants need to be explored.

This study aimed to overcome the subjective nature of routine assessment of knee laxity and develop a repeatable, objective method using a hand-held force application device (FAD).

Eighteen clinicians (physiotherapists, consultants, trainees) volunteered to measure the coronal angular deviation of the right knee of a healthy volunteer using a validated non-invasive infrared measuring system. Effort was taken to ensure the knee flexion angle (∼2°) and hand positions were constant during testing. Three varus and valgus stress tests were conducted, in which maximum angular deviation was determined and subsequently averaged, in the following order of conditions: manual stress without the FAD up to a perceived end-point (before); with the FAD to apply a moment of 18 Nm; and again without the FAD (after). A repeated measures ANOVA was used to analyse the results.

All three groups of clinicians produced measurements of valgus laxity with consistent mean values and standard deviations (<1°) for each condition. For varus mean values were consistent but standard deviations were larger.

Valgus deviations varied significantly between conditions (p < 0.01), with deviations achieved using the FAD greater than both before (p < 0.01) and after (p < 0.05) indicating that the perceived endpoints were less than that achieved at 18 Nm. However varus perceived endpoints were no different to that achieved at 18 Nm, suggesting that clinicians usually apply a greater valgus moment than varus. Furthermore, the non-significant increase in valgus deviation between before and after (p = 0.123) is suggestive of a training trend, especially for trainees.

Our standardised knee laxity assessment may have a role in improving the balancing techniques of TKA and the diagnosis of collateral ligament injuries. Also, by quantifying the technique of senior clinicians, and with use of the FAD, the perceptive skills of more junior trainees may be enhanced.

Clinical laxity tests are frequently used for assessing knee ligament injuries and for soft tissue balancing in total knee arthroplasty (TKA). Current routine methods are highly subjective with respect to examination technique, magnitude of clinician-applied load and assessment of joint displacement. Alignment measurements generated by computer-assisted technology have led to the development of quantitative TKA soft tissue balancing algorithms. However to make the algorithms applicable in practice requires the standardisation of several parameters: knee flexion angle should be maintained to minimise the potential positional variation in ligament restraining properties; hand positioning of the examining clinician should correspond to a measured lever arm, defined as the perpendicular distance of the applied force from the rotational knee centre; accurate measurement of force applied is required to calculate the moment applied to the knee joint; resultant displacement of the knee should be quantified.

The primary aim of this study was to determine whether different clinicians could reliably assess coronal knee laxity with a standardised protocol that controlled these variables. Furthermore, a secondary question was to examine if the experience of the clinician makes a difference. We hypothesised that standardisation would result in a narrow range of laxity measurements obtained by different clinicians.

Six consultant orthopaedic surgeons, six orthopaedic trainees and six physiotherapists were instructed to assess the coronal laxity of the right knee of a healthy volunteer. Points were marked over the femoral epicondyles and the malleoli to indicate hand positioning and give a constant moment arm. The non-invasive adaptation of a commercially available image-free navigation system enabled real-time measurement of coronal and sagittal mechanical femorotibial (MFT) angles. This has been previously validated to an accuracy of ±1°. Collateral knee laxity was defined as the amount of angular displacement during a stress manoeuvre. Participants were instructed to maintain the knee joint in 2° of flexion whilst performing a varus-valgus stress test using what they perceived as an acceptable load. They were blinded to the coronal MFT angle measurements. A hand-held force application device (FAD) was then employed to allow the clinicians to apply a moment of 18Nm. This level was based on previous work to determine a suitable subject tolerance limit. They were instructed to repeat the test using the device in the palm of their right hand and to apply the force until the visual display and an auditory alarm indicated that the target had been reached. The FAD was then removed and participants were asked to repeat the clinical varus-valgus stress test, but to try and apply the same amount of force as they had been doing with the device.

Maximum MFT angular deviation was automatically recorded for each stress test and the maximum moment applied was recorded for each of the tests using the FAD. Means and standard deviations (SD) were used to compare different clinicians under the same conditions. Paired t-tests were used to measure the change in practice of groups of clinicians before, during and after use of the FAD for both varus and valgus stress tests.

All three groups of clinicians initially produced measurements of valgus laxity with consistent mean values (1.5° for physiotherapists, 1.8° for consultants and 1.6° for trainees) and standard deviations (<1°). For varus, mean values were consistent (5.9° for physiotherapists, 5.0° for consultants and 5.4° for trainees) but standard deviations were larger (0.9° to 1.6°). When using the FAD, the standard deviations remained low for all groups for both varus and valgus laxity. Introducing the FAD overall produced a significantly greater angulation in valgus (2.4° compared to 1.6°, p<0.001) but not varus (p = 0.67) when compared to the initial examination. In attempting to reach the target moment of 18Nm, the mean ‘overshoot’ was 0.9Nm for both varus and valgus tests. Standard deviations for varus laxity were lower for all groups following use of the FAD. The consultants' performance remained consistent and valgus assessment remained consistent for all groups. The only statistically significant change in practice for a group before and after use of the FAD was for the trainees testing valgus, who may have been trained to push harder (p = 0.01). Standardising the applied moment indicated that usually a lower force is applied during valgus stress testing than varus. This was re-enforced by clinicians, one third of whom commented that they felt they had to push harder for valgus than varus, despite the FAD target being the same.

We have successfully standardised the manual technique of coronal knee laxity assessment by controlling the subjective variables. The results support the hypothesis of producing a narrow range of laxity measurements but with valgus laxity appearing more consistent than varus. The incorporation of a FAD into assessment of coronal knee laxity did not affect the clinicians' ability to produce reliable and repeatable measurements, despite removing the manual perception of laxity. The FAD also provided additional information about the actual moment applied. This information may have a role in improving the balancing techniques of TKA and the management of collateral ligament injuries with regard initial diagnosis and grading as well as rehabilitation.

Finally, the results suggest that following use of the FAD, more experienced clinicians returned to applying their usual manual force, while trainees appeared to use this augmented feedback to adapt their technique. Therefore this technique could be a way to harness the experience of senior clinicians and use it to enhance the perceptive skills of more junior trainees who do not have the benefit of this knowledge.

As well as improved component alignment, recent publications have shown that navigation systems can assess knee kinematics and provide a quantitative measurement of soft tissue characteristics. In particular, navigation-based measures of varus and valgus stress angles have been used to define of the extent of soft-tissue release required at the time of the placement of the prosthesis. However, the extent to which such navigation-derived stress angles reflect the restraining properties of the collateral ligaments of the knee remain unknown. The aim of this cadaveric study was to investigate correlations between the structural properties of the collateral ligaments of the knee and stress angles measured with an optically-based navigation system.

Nine fresh-frozen cadaveric knees (age 81 ± 11 years) were resected 10-cm proximal and distal to the knee joint and dissected to leave the menisci, cruciate ligaments, posterior joint capsule and collateral ligaments. The resected femoral and tibial were rigidly secured within a test system which replicated the lower limb and permitted kinematic registration of the knee using the standard workflow of a commercially available image free navigation system. Frontal plane knee alignment and varus-valgus stress angles in extension were acquired. The manual force required to produce varus-valgus stress angles during clinical testing was quantified with a dynamometer attached to the distal tibial segment. Following assessment of knee laxity, bone–ligament–bone specimens were prepared and mounted within a uniaxial materials testing machine. Following 10 preconditioning cycles specimens were extended to failure. Force and crosshead displacement were used to calculate principal structural properties of the ligaments including ultimate tensile strength and stiffness as well as the instantaneous stiffness at loads corresponding to those applied during varus-valgus stress testing. Differences in the structural properties of the collateral ligaments and the varus and valgus laxity of the knee were evaluated using paired t tests, while potential relationships were investigated with scatter plots and Pearson’s product moment correlations.

There was no significant difference in the mean varus (4.3 ± 0.6°) and valgus laxity measured (4.3 ± 2.1°) for the nine knees or the corresponding distal force application required during stress testing (9.9 ± 2.5N and 11.1 ± 4.2N, respectively). Six of the nine knees had a larger varus stress angle compared to the valgus angle. There was no significant difference in the stiffness of the medial (63 ± 15 N/mm) and lateral (57 ± 13 N/mm) collateral ligaments during failure testing. The medial ligament, however, was approximately two fold stronger than its lateral counterpart (780 ± 214N verse 376 ± 104N, p< 0.001). While the laxity measures of the knee were independent of the ultimate tensile strength and stiffness of the collateral ligaments, there was a significant correlation between the force applied during stress testing and the instantaneous stiffness of the medial (r = 0.91, p = 0.001) and lateral (r = 0.68, p = 0.04) collateral ligaments.

The findings of the current study suggest that computer-assisted measures of passive knee laxity are largely independent of the ultimate strength and stiffness of the collateral ligaments. The force applied during manual stress testing of the knee, however, was strongly correlated with the instantaneous stiffness of the collateral ligaments suggesting users may attend to the low-stress behaviour of the ligaments. Nonetheless the force applied during stress testing varied between knees, as did the resultant angular deviation. Therefore to make use of the quantified data given by navigation systems, further work to understand the relationships between applied force, resultant stress angles and clinical outcomes for knee arthroplasty is required.

Degeneration of the intervertebral disc results in patent cracks [1] and a decrease in osmotic pressure associated with loss of fixed charges. The relationship between mechanical load and damage in the disc is very poor [2]. This finding is at odds with physical intuition. The subject of this study is relationship between the development of patent cracks and the decrease in osmotic pressure in the degenerating disc in the light of the physics of swelling [3–7]. We restrict the experimental part of this study to hydrogel, thus avoiding complications associated with biological variability. The finite element modelling [6,7] used in this study catches salient features of stress profiles measured by Mc Nally and al.

Thin hydrogel samples with a crack of 5 mm are used. The crack opens as a result of decreasing osmotic pressure in the experiments and in the simulation. The initial uniform stress distribution turns into a distribution with a decreased average stress level and a high stress around the crack tip. A decrease in osmotic pressure opens an existing crack in swelling materials independently from external mechanical load. Hence, disc degeneration causes the overall stress to decrease, while local stress around a crack tip increases. This mechanism may explain why damage in the disc is so poorly correlated with mechanical load [3] and why the degenerated disc is characterized by patent cracks [1]. The process of crack opening in the degenerating disc is comparable to the crack development in an aging oaken beam, while loosing its turgor.

Introduction: In vivo measurements of intradiscal stresses are difficult. McNally measured stress profiles in human discs. It is unclear why some exhibit stress peaks in posterior annulus while others do not. Therefore finite element (FE) models are useful to improve the knowledge of stress distribution in the disc. We compared experimental and numerical stress in discs under axial loading, in non degenerated and degenerated disc.

Methods: The FE disc model resembles one fourth of a full disc. The annulus contains both matrix and fibers, while the nucleus only consists of matrix. Similar load profiles were applied and model predictions of matrix stress were compared to experiments (stress profilometry).

Results: Both experimental data and numerical simulations exhibit a peak of axial stress in posterior annulus and lower peaks in anterior annulus. Simulating a “normal” disc results in a uniform matrix stress profile from posterior to anterior. By reducing the fixed charged density (FCD) to 50% in both nucleus and annulus, stress profiles become non-uniform. Stresses in the nucleus decrease. Axial annulus stresses exhibit peaks on anterior and posterior side. Stress peaks increase when FCD decrease under the same loading.

Discussion: The size of the peaks computationally depends on the FCD in discs. Decreasing the FCD shows development of stress peaks in the annulus. A uniform stiffness is seen in nucleus region, but not in annulus. The hydrostatic pressure, due to the FCD, is not high enough to evenly distribute the load over the whole disc. The posterior stress peaks may explain why hernia develops particularly in the posterior annulus.