Fluid film lubricating ability of a total hip prosthesis depends on the profile accuracies including surface-roughness or the sphericity of a head or a cup. Therefore, surface polishing is important. It was, however, difficult to polish the central portion of a cup or head using the conventional rotating machine. In the present study, we developed a polishing method combining a pendulum machine and a robotic arm. The effect of the accuracy improvement by this method was evaluated by the friction measurements on some test specimens. Nine balls and a cup of Co-Cr-Mo alloy that were polished by a conventional process using a rotating machine were prepared for the prototype. The average diameter of the balls was 31.9648 mm with the sphericity of 0.0028 μm. The inside diameter of the cup was 31.9850 mm with the sphericity of 0.0044 μm. We combined a robotic arm and a pendulum apparatus to enable the further polishing. The ability of both automatic centering and change in the sliding direction was accomplished by this system. The sliding direction has been changed 180 times every ten degrees. The total distance of polishing was 120 m under vertical load of 100 N in a bath of saline solution containing abrasive grains of silicate of the diameter of 2μm. The surface roughness of the central portion of the cup, which is important area for the fluid film lubrication decreased from Ra 20.2 μm before the polishing to Ra 18.7 μm after the polishing. A pendulum type friction tester was used for the assessment of the improvement of the lubricating ability by the polishing. The measurement was run over at 10 times under the conditions of the load of 600 N in a bath of saline solution. As the result, the frictional coefficients decreased from 0.1456–0.1720 before polishing to 0.1250–0.1300 after polishing. The polishing effect was, however, observed only at the specimens that radial clearances did not exceed the value of 50 μm. The present results indicated that the surface polishing of the central portion of hip prostheses must improve the lubrication ability and the radial clearance before the finishing process should be chinked as possible

Aims. The optimum clearance between the bearing surfaces of hip arthroplasties is unknown. Theoretically, to minimize wear, it is understood that clearances must be low enough to maintain optimal contact pressure and fluid film lubrication, while being large enough to allow lubricant recovery and reduce contact patch size. This study aimed to identify the relationship between diametrical clearance and volumetric wear, through the analysis of retrieved components. Methods. A total of 81 metal-on-metal Pinnacle hips paired with 12/14 stems were included in this study. Geometrical analysis was performed on each component, using coordinate and roundness measuring machines. The relationship between their as-manufactured diametrical clearance and volumetric wear was investigated. The Mann-Whitney U test and unpaired t-test were used, in addition to calculating the non-parametric Spearman's correlation coefficient, to statistically evaluate the acquired data. Results. The hips in this study were found to have had a median unworn diametrical clearance of 90.31 μm (interquartile range (IQR) 77.59 to 97.40); 32% (n = 26) were found to have been below the manufacturing tolerance. There was no correlation found between clearance and bearing (r. s. = -0.0004, p = 0.997) or taper (r. s. = 0.0048, p = 0.966) wear rates. The wear performance of hips manufactured within and below these specifications was not significantly different (bearing: p = 0.395; taper: p = 0.653). Pinnacles manufactured from 2007 onwards had a greater prevalence of bearing clearance below tolerance (p = 0.004). Conclusion. The diametrical clearance of Pinnacle hips did not influence their wear performance, even when below the manufacturing tolerance. The optimum clearance for minimizing hip implant wear remains unclear. Cite this article: Bone Joint Res 2020;9(8):515–523

Metal ion concentrations following metal on metal hip resurfacing arthroplasty remain a concern. Variables associated with increased metal ion concentrations need to be established. This study provides metal ion data from a consecutive cohort of the first 76 patients implanted with a fourth generation hip resurfacing prosthesis. All patients agreed to post-operative blood metal ion sampling at a minimum of one year. Post-operative radiographic measurements of cup inclination and anteversion were obtained using the EBRA software. Mean whole blood chromium (Cr) and cobalt (Co) concentrations in patients receiving the smallest femoral implants (Ł51mm) were greater than in the patients implanted with the largest prostheses (ł53mm) by a factor of 3 and 9 respectively. Ion concentrations in the small femoral group were significantly related to acetabular inclination (R=0.439, P< 0.001 for Cr, R=0.372, P=0.004 for Co) and anteversion (R=0.330, P=0.010 for Cr, R=0.338, P=0.008 for Co). This relationship was not significant in the large implant group. Mean Cr and Co concentrations in patients with accurately orientated cups (inclination < 45°, anteversion < 20°) were 3.7μg/l and 1.8 μg/l respectively, compared to 9.1μg/l and 17.5μg/l in malaligned cups. A reduced surface contact area caused by cup malalignment may increase contact stresses, resulting in a high wear rate if fluid film lubrication is inadequate. Improved fluid film lubrication has previously been found in larger heads in vitro. Accurate acetabular component positioning is essential in order to reduce metal ion concentrations following hip resurfacing

Purpose of study There is renewed scientific interest in the use of metal-metal bearings for hip replacements. Such bearings have lower volumetric wear rates compared to metal or ceramic on polyethylene bearings. They permit the use of large diameter bearings which potentially have the benefit of reduced dislocation. They also allow the use of thin components without the risk of fracture associated with similar ceramic-ceramic components. However, there remain concerns about the long-term effects of nanometre sized debris and the release of metal ions. It is therefore critical to understand which parameters are important in minimising the amount of debris generated. This study investigated the effect of design and materials on the wear rates in a hip simulator. Methods Wear studies were carried out in a 10 station ProSim hip simulator in 25% newborn calf serum. A Paul type load curve was applied (maximum load 3000N, minimum 300N) in an anatomical configuration. The extent of a fluid film between the bearing surfaces was determind by measuring the voltage drop between the components. Test samples were made from low-carbon (< 0.05%) and high-carbon (> 0.20%) CoCrMo alloys in various conditions. These samples had bearing surface diameters of 16–54.5mm. The diametral clearance between the femoral head and acetabular cups were from 50–300um. Results The results of this study were that the low-carbon material wears more than high-carbon materials, there is no significant difference in wear performance of the various forms of high-carbon material tested (wrought, cast, and cast and heat treated), and wear decreased with reduced clearances and increased component diameter. Voltage changes indicated that reduced clearances resulted in component separation and fluid film lubrication. Conclusions These results are consistent with the hypothesis that large diameter metal-on-metal bearings with optimized bearing surface geometry operate in the mixed and/or fluid film lubrication regime

Polyimide (MP-1, MMATech, Haifa, Israel), is a high performance aerospace thermoplastic used for its lubricity, stability, inertness and radiation resistance. A wear resistant thin robust bearing is needed for total hip arthroplasty (THR). After independent laboratory testing, in 2006, the author used the material as a bearing in two Reflection (Smith and Nephew, USA) hip surgeries. The first, a revision for polyethylene wear, survives with no evidence of wear, noise, new osteolysis or complications related to the MP-1 bearing after 16 yrs. The second donated his asymptomatic MP-1 hip at 6.5yrs for post-mortem examination. There were no osteoclasts, cellular reaction bland in contrast to that of polyethylene. In 2013 a clinical study with ethical committee approval was started using a Biolox Delta (Ceramtec, Germany) head against a polyimide liner in 97 patients. MMATech sold all liners, irradiated: steam 52:45. Sixteen were re-machined in New Zealand. Acetabular shells were Delta PF (LIMA, Italy). The liner locked by taper. The cohort consisted of 46:51 M:F, and ages 43 to 85, mean 65. Ten received cemented stems. For contralateral surgery, a ceramic or polyethylene liner was used. Initial patients were lower demand, later, more active patients, mountain-biking and running. All patients have on-going follow up, including MP-1 liner revision cases. There has been no measurable wear, or osteolysis around the acetabular components using weight-bearing radiographs. Squeaking within the first 6 weeks was noted in 39 number of cases and subtle increase in palpable friction, (passive rotation at 50 degrees flexion), but then disappeared. There were 6 revisions, four of which were related to cementless Stemsys implants (Evolutis, Italy) fixed distally with proximal linear lucencies in Gruen zones 1 and 7, and 2 and 6. No shells were revised and MP-1 liners were routinely changed to ceramic or polyethylene. The liners showed no head contact at the apex, with highly polished contact areas. There were no deep or superficial infections, but one traumatic anterior dislocation at 7 years associated with 5 mm subsidence of a non-collared stem. The initial squeaking and increased friction was due to the engineering of the liner / shell composite as implanted, not allowing adequate clearance for fluid film lubrication and contributed to by shell distortion during impaction. The revised bearings were “equatorial” rather than polar, and with lack of wear or creep this never fully resolved. Where the clearance was better, function was normal. The “slow” utilization was due to my ongoing concern with clearances not being correct. The revision of 4 Stemsys stems, tribology issues may have contributed, but non “MP-1” / Stemsys combinations outside this study have shown the same response, thought to be due to de-bonding of the hydroxyapatite coating. With correct engineering and clearances, a 3.6 mm thick MP-1 bearing, a surface Ra<0.5, steam sterilized, shows no appreciable wear, and with confidence, can be used as a high performance THR bearing

Resurfacing metal-on-metal hip arthroplasty is currently showing promising clinical results. However there are concerns related to such implants, including the elevated levels of metal ions typically seen in patients. Valuable data can be obtained from explanted prostheses but due to their recent introduction few retrieval studies on resurfacing hip prostheses have been published. Five ASR hip resurfacing prostheses were revised due to pain. From two patients, head and cup were available for independent explant analysis. In the other three cases only femoral components were available. All were removed from female patients and all were revised to ceramic-on-ceramic hip prostheses. Post-operative radiographic measurements of cup inclination and ante-version were obtained using the EBRA software. The surface roughness values of the articulating surfaces of the explants were measured using a non-contacting profilometer. A co-ordinate measuring machine was used to measure the diameter of the head and the cup and thus the diametral clearance. The same measurements were then taken from a new unused ASR prosthesis and compared. Using elastohydrodynamic theory the minimum effective film thickness of the implant was calculated. In turn this allowed the lubrication regime to be determined. The average roughness values of the head and the cup of one implant were found to be 0.135microns and 0.058microns respectively, with a diametral clearance of 110microns. These results indicated that, at the time of removal, the prosthesis would have operated in the boundary lubrication regime. Other explants showed evidence of localised contact between the head and the rim of the acetabular cup, and these showed articulating surfaces with typical roughness values of between 0.025microns and 0.050microns. The new ASR had head and cup surface roughness values of 0.010microns and 0.012microns respectively and a diametral clearance of 87microns, implying that a new implant would operate under fluid film lubrication. All cups five were implanted with inclination angles over 45 degrees and anteversion over 25 degrees. These results suggest that components with high inclination and anteversion angles display greater than expected wear and may operate in boundary rather than fluid film lubrication which may eventually lead to early failure

Squeaking in ceramic on ceramic bearing total hip arthroplasty is well documented but its aetiology is poorly understood. In this study we have undertaken an acoustic analysis of the squeaking sound recorded from 31 ceramic on ceramic bearing hips. The frequencies of these sounds were compared with in vitro acoustic analysis of the component parts of the total hip implant. Analysis of the sounds produced by squeaking hip replacements and comparison of the frequencies of these sounds with the natural frequency of the component parts of the hip replacements indicates that the squeaking sound is due to a friction driven forced vibration resulting in resonance of one or both of the metal components of the implant. Finite element analysis of edge loading of the prostheses shows that there is a stiffness incompatibility between the acetabular shell and the liner. The shell tends to deform, uncoupling the shell-liner taper system. As a result the liner tends to tilt out of the acetabular shell and slide against the acetabular shell adjacent to the applied load. The amount of sliding varied from 4–40μm. In vitro acoustic and finite element analysis of the component parts of a total hip replacement compared with in vivo acoustic analysis of squeaking hips indicate that either the acetabular shell or the femoral stem can act as an “oscillator’ in a forced vibration system and thus emit a squeak. Introduction: Squeaking has long been recognized as a complication in hip arthroplasty. It was first reported in the Judet acrylic hemiarthroplasty. 1. It was the squeak of a Judet prosthesis that led John Charnley to investigate friction and lubrication of normal and artificial joints which ultimately led to the concept of low friction arthroplasty. Ceramic on ceramic bearings were pioneered by Boutin in France during the 1970’s, but experienced unacceptably high fracture rates. Charnley demonstrated in vitro squeaking when he tested one of Boutin’s ceramic-on-ceramic bearings in his pendulum friction comparator. 2. Squeaking has also been reported in other hard on hard bearings, and can also occur after polyethylene bearing surface failure resulting in articulation between metal on metal or ceramic on metal surfaces. 3–6. Recently, squeaking has been increasingly reported in modern ceramic-on-ceramic bearings in hip arthroplasty. However, although well-documented, the aetiology of squeaking in ceramic on ceramic bearings is still poorly understood. The incidence ranges from under 1% to 10%. 7–10. It has been reported in mismatched ceramic couples,11and after ceramic liner fracture. 12,13. An increased risk of squeaking has been demonstrated with acetabular component malposition, as well as in younger, heavier and taller patients. 9. However, it may also occur in properly matched ceramic bearings with ideal acetabular component position and in the absence of neck to rim impingement. 7–9. In rare cases, the squeak is not tolerated by the patient and has prompted a revision. Under ideal conditions hard-on-hard bearings are assumed to be operating under conditions of fluid film lubrication with very low friction. 14,15. However, if fluid film lubrication breaks down leading to dry sliding contact there will be a dramatic increase in friction. If this increased friction provides more energy to the system than it can dissipate, instabilities may develop in the form of friction induced vibrations and sound radiation. 16. Friction induced vibrations are a special case of forced vibration, where the frequency of the resulting vibration is determined by the natural frequency of the component parts. Running a moistened finger around the rim of a wine glass is an example of this. [Appendix]. The hypothesis of this study is that the squeaking sound that occurs in ceramic on ceramic hip replacement is the result of a forced vibration. This forced vibration can be broken down into a driving force and a resultant dynamic response. 17. The driving force is a frictional driving force and occurs when there is a loss of fluid film lubrication resulting in a high friction force. 14,15,18. The dynamic response is a vibration of a part of the device (the oscillator) at a frequency that is influenced by the natural frequency of the part. 16. By analyzing the frequencies of the sound produced by squeaking hip replacements and comparing them to the natural frequency of the component parts of a hip replacement this study aims to determine which part produces the sound. Materials and methods: In vitro determination of the natural frequencies of implant components Modal analysis has suggested that resonance of the ceramic components would occur only at frequencies above the human audible range and that resonance of the metal parts would occur at frequencies within the human audible range. Furthermore, that resonance of the combined ceramic insert and titanium shell would not be within the human audible range. To test this hypothesis we performed a simple acoustic analysis. The natural frequency of hip replacement components was determined experimentally using an impulse-excitation method (Grindo-sonic). Components were placed on a soft foam mat in a quiet environment and struck with a wooden mallet. The sound emitted from the component was recorded on a personal computer with an external microphone with a frequency response which ranges from 50Hz to 18,000Hz (Beyerdynamic MCE87, Heilbronn, Ger-many). The computer has an integrated sound card with a frequency response from 20Hz to 24kHz (SoundMAX integrated digital audio chip, Analogue Devices Inc, Norwood, M.A.) and we used a codec with a frequency response from 20Hz to 20kHz (Audio Codec ’97, Intel, Santa Clara, CA). Sound files were captured as 16 bit mono files at a sample rate of 48000Hz using acoustic analysis software (Adobe Audition 1.5, Adobe Systems Incorporated, San Jose, California, USA). We performed fast Fourier transform (FFT) of the sound using FFT size 1024 with a Blackmann-Harris window to detect the frequency components of the emitted sound. (Fast Fourier transform is an accepted and efficient algorithm which enables construction of a frequency spectrum of digitized sound). We tested the following components: modular ceramic/titanium acetabular components, which included testing the titanium shell and the respective ceramic inserts both assembled according to the manufacturer’s instructions and unassembled; titanium femoral stems and ceramic femoral heads both assembled and unassembled. A range of sizes of each component was tested according to availability from our retrieval collection. In vivo acoustic analysis: Sound recordings were collected from 31 patients. Nineteen recordings were made at our institution: 16 of these were video and audio recordings and 3 were audio only recordings. Video recording was with a digital video camera recorder (Sony DCR-DVD101E Sony Electronics, San Diego, CA, USA) with the same external microphone used in the in vitro analysis. For 3 patients who could not reproduce the sound in the office we lent them a digital sound recorder for them to take home and record the sound when it occurred (Sony ICD-MX20, Sony Electronics, San Diego, CA, USA). This device has a In vivo acoustic frequency range from 60Hz to 13,500Hz. The remainder of the recordings were video and audio recordings made by surgeons at three other institutions on digital video camera recorders. Sound files were captured and analyzed by the same method used in the in vitro analysis. Each recording was previewed in the spectral view mode which allows easy visual identification of the squeak in the sound recording. In addition all sound recordings were played, listening for the squeak. Once a squeak was identified a fast Fourier transform (FFT) was performed. We used FFT size 1024 with a Blackmann-Harris window which allowed us to easily pick out the major frequency components. All prominent frequency components were recorded at the beginning of the squeak and at several time points during the squeak if there was any change. A range was recorded for the fundamental frequency component. We were able to determine the frequency range of the recording device used by observing the frequency range of the background noise on the recording. We found that if a squeak was audible on the recording we had no difficulty determining its frequency regardless of the quality of the device used to make the recording or the amount of background noise. The mean age of the patients was 54 years (23 to 79 years), mean height was 171cm (152 to 186cm) and mean weight was 79kg (52 to 111kg). There were 17 female and 14 male patients. There were nineteen ABGII stem and ABGII cup combinations, 10 accolade stem and trident cup, 1 Exeter stem and trident cup and 1 Osteonics Securfit stem with an Osteonics cup. Ethics committee approval was obtained for this project from our institution and from the referring institutions and informed consent was gained from the patients. Finite element analysis of edge loading: Edge-loading wear which may provide a mechanism for failure of fluid film lubrication and may therefore play a role in squeaking. To evaluate edge loading further we conducted finite-element analysis (FEA). 9. Computed tomography (CT) scans of an intact pelvis were obtained from visual human data set (VHD, NLM, Bethesda, Maryland). Slices were taken at 1mm thick with no inter-slice distance through the entire pelvis. The CT files were then read into a contour extraction program and saved into an IGES file format which was imported into PATRAN (MSC Software, Los Angeles, CA) to develop the pelvic geometry. The pelvis was meshed with 10 noded modified tetrahedral elements. The model was reconstructed with a 54mm titanium alloy generic acetabular shell and a 28mm alumina ceramic liner. The acetabular shell and ceramic liner were meshed using 8 noded hexahedral elements. The shell-liner modular taper junction incorporated an 18° angle. The implant contact conditions (Lagrangian multiplier) allowed the liner and shell to slide with a friction coefficient of 0.9. Tied contact conditions were applied between the generic acetabular shell and the bone representing bone ongrowth. Bone material properties were extracted from the CT files by taking the Hounsfield value and the coordinates and mapping to the element in the model allowing us to calculate the Young’s modulus for each element . 19. Material properties for the shell and liner were based on published values. 20. for titanium alloy and alumina ceramic

Introduction: Following hip replacement surgery the tension of the soft tissues and the laxity of the joint may vary. Variations in surgical approach, technique and fixation method may influence the effective joint laxity and the level of force applied across the prostheses during the swing phase of gait. The aim of this study was to investigate the effect of different swing phase load conditions on the wear metal-on-metal hip prostheses using a hip simulator. Methods: Cobalt chrome metal-on-metal bearings, 28mm in diameter were tested for five million cycles in a Prosim hip simulator with flexion-extension and internal-external rotation kinematic inputs. A Paul-type twin peak loading curve was applied, which was modified to provide three different swing phase load conditions;. Low positive swing phase load (< 100N). Positive swing phase load (300N, as per standard ISO 14242–1). Negative swing phase load, leading to microseparation and joint laxity. All tests were carried out in 25% (v/v) new-born bovine serum, with gravimetric wear measurements completed every million cycles. Results: The wear rates for the different swing phase conditions are shown in Figure I. Elevating the swing phase load from 100N to 300N (ISO load) increased the overall wear rate by 10-fold. Introducing microseparation into the gait cycle increased wear by a further 3-fold. These results indicate the sensitivity of metal-on-metal bearing wear to swing phase load conditions and joint laxity. Discussion: Little attention to date has been paid to the importance of joint laxity and swing phase load on the wear rate of hip replacements. Elevation of wear rates with increased swing phase load was probably due to the depletion of fluid film lubrication. This was consistent with the findings under stop-start motion [Medley et al., 2002] and demonstrates the dependency of metal-on-metal hip replacements on fluid film lubrication conditions. Testing with a negative swing phase load elevated wear due to microseparation of the components, the head contacted the insert rim at heel strike which caused a stress concentration and damage to the insert rim. The results demonstrate that the wear performance of metal-on-metal hip replacements is highly dependent on swing phase load conditions. It is postulated that the fixation method and surgical technique can effect the swing phase load; over tensioning of the soft tissue may increase the swing phase load, whereas joint laxity will cause a negative swing phase load and possibly microseparation

Introduction: Hip simulator and clinical retrieval studies have shown that metal-on-metal (MOM) hip implants commonly have biphasic wear. An initial high wear or running-in phase is generally followed by a low wear or steady-state phase. A number of hypotheses have been put forward to explain this biphasic phenomenon, including polishing of the metallic bearing surfaces and increasing conformity between the two articulating surfaces. The purpose of the present study was to compare the wear and lubrication of MOM hip implants between the running-in and steady-state periods. Materials and Methods: A standard 28mm Metasul. TM. MOM bearing (Centerpulse Orthopedics, a Zimmer Company, Winterthur, Switzerland) was investigated. The wear testing was carried out using a 6-station AMTI hip simulator in the presence of 33% bovine serum and 67% Ringer solution (PH 7.2). The bearing surfaces of both the femoral and acetabular components were measured using a coordinate measurement machine at different stages of wear testing. The dimensional changes of the bearing surfaces due to wear were directly incorporated into the elastohydrodynamic lubrication analysis using an in-house developed code. Results: The initial running-in period occurred during the first 1 million cycles, and little wear was observed subsequently up to 5 millions cycles. The maximum total wear depth was measured to be around 13 μm at 1 million cycles. The predicted average lubricant film thickness between the two articulating surfaces was increased from 0.024μm at the beginning, to 0.09μm at the end of the first 1 million cycles. For a given composite surface roughness of 0.03μm often quoted for the metallic bearing surfaces, such an increase in the lubricant film thickness represents a transition from a mixed to a fluid film lubrication regime. Discussion: A large improvement in lubrication was predicted as a direct result of the running-in wear of the bearing surfaces. This was mainly due to the increased conformity between the two articulating surfaces and the decreased diametrical clearance. It was particularly noted that the improvement in lubrication after 1 million cycles was so significant that continuous fluid film lubrication was possible, leading to extremely low wear for up to 5 million cycles, and only material fatigue and start-up and stopping for wear measurements could cause a further increase in wear. It is possible in theory to optimise the geometry of the metallic bearing surfaces, based on the worn components, to minimise the running-in wear. However, such an improvement in lubrication cannot be readily achieved because of difficulties in surgical techniques and position of the components

Hip resurfacing using metal-on-metal bearings has a number of purported advantages over traditional total hip replacement in the young, active patient. Males in particular can benefit from the bone preservation, stability, and higher activity levels seen with this procedure. As more is learned about the factors affecting long-term outcome of hip resurfacing, component position has emerged as one major predictor of success. Given a well-selected patient, and a well-designed device, acetabular positioning is perhaps the most important determinant of long-term survivorship in hip resurfacing. One feature of resurfacing socket design which has not been widely disseminated is the sub-hemispheric arc of the bearing surface. While the outer circumference of the socket represents a complete hemisphere, and radiographic evaluation may assume that the apparent socket angle is satisfactory, the actual bearing is less than a hemisphere, so that the true abduction of the bearing is considerably more vertical. This important fact leads to excessive bearing inclination, edge loading, and all that follows, including runaway wear, metallosis, ALVAL, and pseudotumors. Inadequate socket anteversion can expose the psoas tendon to abrasion and tendonitis. Too much acetabular anteversion, especially when combined with increased femoral neck anteversion, can result in an overall decrease in bearing contact area, and excessive wear. Femoral component positioning is critical in the prevention of femoral neck fractures, which are a chief cause of early failure. Varus placement increases the tensile stresses on the superior femoral neck. Excessive valgus threatens notching. Both increase femoral neck fractures. Sufficient malposition will ultimately result in edge loading. Edge wear is incompatible with fluid film lubrication, the key to longevity of these bearings

Introduction. Metal-on-polycarbonate urethane (MPU) is a cutting-edge new bearing technology for hip arthroplasty. The acetabular component consists of a 2.7mm-thick polycarbonate-urethane liner inserted into a specially manufactured uncemented titanium shell coated with hydroxyapatite [(HA) Fig. 1]. The liner is pliable and biomechanically mimics human cartilage. In vitro studies have shown minimal wear, fluid film lubrication, physiological load transmission and shock absorption capacity equal to the normal hip. This system includes prosthetic heads of a diameter 12mm less than the socket diameter. The aim of this study was to clinically assess patients treated with this novel technology in a retrospective single centre study. Methods. Twenty-seven patients with osteoarthritis treated with MPU bearing arthroplasty were included. Mean patient age was 67.9±10.35 years (44–84). Sixteen patients were female and 11 were male. Twenty-four of these had an uncemented HA-coated stem while 3 had a hip resurfacing metal femoral component. All patients were operated on by a single surgeon using a postero-lateral approach. Results. No patients were lost to follow-up. Mean follow-up time was 29 months (minimum 24 months). There were no major complications. At follow-up, the mean Harris hip score was 98 points (80–99). X-rays showed good bone-implant contact without any osteolysis or bone rarefaction. Discussion and conclusion. Our promising short-term results confirm the in vitro findings. Advantages of this new bearing technology include the possibility to use large diameter metal heads without exposing the patients to elevated levels of metal ions as is the case with metal-on-metal bearings, the minimal wear and the superior biomechanical characteristics

The ACCIS system comprises a bearing of a 5 micron surface ceramic upon a Chrome Cobalt Molybdenum (CrCoMo) substrate which allows for a homogeneous couple. The Titanium Niobium Nitride (TiNbN) microceramic applied by Plasma Vapour Deposition. In comparison with CrCoMo alloy, TiNbN gives a hard (2800 vs 489V), smooth (0.23 vs 0.55Rz), low friction (0.079–0.1 vs 0.11–0.56mu pin on disk test), wetable surface which when combined allows for the potential of gaining fluid film lubrication (lambda>3) on a smaller head diameter than an untreated surface. These properties are postulated to reduce wear and hence lower the release of Cr and Co ions in vivo. The surface microceramic also prevents exposure to release of Cr and Co by corrosion. The surface modified implants were first used in 2003 in large head arthroplasty and later in 2005 with resurfacing implants. Two series of patients implanted by a single surgeon were examined to elucidate the metal ion release of the ACCIS system. The first series retrospectively examined 52 consecutive Large Head Arthroplasty cases for [Cr], [Co] and [Mo] levels. A mean follow-up time of 7.5 yrs (77–101mths) with 9 patients being lost to revision and death by the time of the study. Median levels of [Cr] 1.6, [Co] 4.76 and [Mo] 2.5 µg/l were obtained. The second series prospectively examined the [Cr] and [Co] levels with the pre-operative values as controls in 125 resurfacing cases with the ACCIS microceramic. The second series gave no rising trend observed at up to 5 years ([Cr & Co] (range < 0.5–1.6 µg/l). It is postulated that the ACCIS surface microceramic reduces wear and also reduces the effective patch size for a given load thus allowing for a greater Patch to Edge Distance allowing a greater tolerance to cup positioning. A RCT is currently underway

Introduction. Because of concerns regarding excessive wear and short-term failures attributed to the metal-on-metal bearings, the use of metal-on-metal hip resurfacing arthroplasty (MOMHRA) has been greatly reduced since 2008, despite great mid-term results for well-designed implants and in certain patient populations. The true cause of excessive wear was then unknown. Therefore, identification of true risk factors for the procedure became paramount to refine indications and improve survivorship outcomes. Methods. Over the last 10 years, a systematic search of the US national library of Medicine and National institutes of health with the key words “metal-on-metal” and hip resurfacing” was conducted and returned 2186 items. Of these items, 862 were deemed relevant to our research purposes and entered in our center's reference database from which this review was performed. Results. Edge loading is the main culprit for high wear and high serum Co and Cr ion concentrations because it disrupts the fluid film lubrication of the device. Computation of the contact patch to rim distance (CPR), an estimate of the joint's functional coverage, is the best predictor of potential edge loading and excessive wear. Both in vivo and in vitro studies show that the wear of well-designed and well-positioned MOM bearings diminishes over time with continued use, an advantage only featured by MOM bearings. Systemic wear-related complications and hypersensitivity to metal once thought to be common are in fact rare occurrences. In addition, metal-related revisions only represent a small portion of the various modes of failure encountered with well-designed HRA. In our series of 1321 hips with only 0.5% lost to follow-up, 11 patients underwent revision surgery for excessive wear or adverse local tissue reaction. All but 2 had mal-positioned acetabular components (CPR distance <10mm). One of these 2 patients had serum cobalt and chromium levels of 13 and 9 µg/L respectively, despite a CPR distance of 18.3 mm, while the other showed a peri-prosthetic fluid collection estimated at 111cc on MRI. Component aseptic loosening (acetabular or femoral) remains, as is also the case for total hip arthroplasty (THA), the leading indication for revision surgery, even though substantial progress has been reported to reduce its incidence. Femoral neck fractures and loosening are associated with the surgeon's learning curve which can be avoided with proper training. The survivorship of the femoral component in our series after implementation of surgical technique changes is 99.2% at 10 years for an overall survivorship of 95.5%. A diagnosis of DDH is associated with a higher failure rate, particularly from socket loosening, while women without risk factors have a survivorship of 98.6% at 15 years. Conclusion. HRA has often been, but should not be associated with the results of large head metal-on-metal THA which often present with a different set of failure mechanisms. Now that most of the risk factors for HRA have been identified, and solutions found, a balanced perspective of its results is needed because the long-term data available validate the low wear of MOM bearings which was predicted in the early hip simulator studies. Considering the tremendous progress made in surgical technique and the advanced tribological knowledge acquired with the last 20 years of investigations related to MOM HRA, all the conditions are present to make this procedure a success for lifetime durability as shown in our series where 44 patients (54 hips) have died without a revision at a mean follow-up time of 9.7 years (range, 1.8 to 19.7). For HRA, when devices with adequate coverage and clearance of the ball by the socket are used, severe developmental dysplasia and inadequate surgical technique are responsible for most failures at 10 to 15 years of follow-up. It is our opinion that the advantages of HRA over THA (such as absence of thigh pain, a low dislocation rate, no taper corrosion, and the preservation of proximal femoral bone mineral density and the ability to maintain high activity levels without penalty) now outweigh the risks of using a MOM bearing

Paratenonitis describes inflammation of the paratenon and commonly presents as an overuse injury. The paratenon is the connective tissue sheath that surrounds tendons - including tendo Achilles, and serves to minimise friction with the outer layer of the tendon, the epitenon. Whilst this conjunction allows the tendon to glide smoothly on muscular contraction, the presentation of paratenonitis typically follows periods of frequent, repetitive musculoskeletal movements; hence, paratenonitis commonly afflicts the elite and, albeit to a lesser extent, amateur athlete. The extent to which friction at the epitenon-paratenon juncture contributes to this tendinopathy remains unclear, and this study is therefore concerned with the coefficient of friction and the lubrication regime. By using a specially designed and validated apparatus, the in vivo paratenon-epitenon conjunction was approximated using bovine flexor tendon paratenon and a glass disc; this is being an equivalent experimental set-up to that used in other studies exploring soft tissue contacts. Bovine synovial fluid was used to lubricate the conjunction at 37 deg C, and the frictional characteristics were analysed over a range of sliding speeds and loads. The coefficient of friction was found to generally lie between 0.1 – 0.01. This range suggests that a system of mixed lubrication applies - where the synovial fluid is causing partial separation of the two surfaces. However, when the data is plotted in the form of a Stribeck curve, the trend suggests that boundary lubrication prevails - where lubrication is determined by surface-bound proteins. The coefficient of friction at the epitenon-paratenon interface appears to be approximately one order of magnitude greater than that typically reported within the healthy synovial joint. Additionally, the synovial joint is thought to exhibit some fluid film lubrication (i.e. total surface separation), whereas the epitenon-paratenon lubrication regime appears to vary only between the inferior mixed and boundary systems - depending on the specific biomechanical conditions. This data would suggest that the coefficient of friction at the epitenon-paratenon interface is relatively high and thus is potentially significant in the incidence of paratenonitis. Such a hypothesis could be of particular interest to sports-medicine and orthopaedic specialists

The clearance between the femoral head and the acetabular cup can significantly affect the lubrication, the wear and the lifetime of metal on metal (MOM) hip joints. The objective of this study was to compare the frictional behaviour of MOM joints with different clearance. Two CoCrMo MOM 50mm diameter hip joints, with a small diametral clearance of 17 microns and a big diametral clearance of 212 microns, were used in this study. The friction measurement was carried on the wear patches of MOM bearings during a long-term wear simulator test. A dynamic trapezoidal-form loading cycle was applied to the femoral head with a minimum load of 100N during the swing phase and a maximum load of 2000N throughout the stance phase. A simple harmonic motion of amplitude +/−24 degree was applied to the femoral head in the flexion-extension plane with a frequency of 1 Hz. The friction torque was measured at 0, 0.8, 1.3, 1.9, 4 and 5.5 million cycles using 6 different viscosities of 25% new born calf serum. The results show that the friction factors (f) of small clearance were generally higher than those of big clearance and this difference became wider with the progress of wear. The lower f of big clearance, especially in the lower range of Sommerfeld number (z) after 5.5 million cycles, is significant and will affect the ultimate performance of prostheses as this range has closer rheological properties to synovial fluid and represents long term wear conditions. At the same time, the friction factors were always higher every time when measured from high z to low z, although this difference became slightly smaller with the progress of wear, which indicates that there is still direct contact between the bearings. The lower friction factor when increasing z, is due to the wear and bedding-in with the progress of the measurement. It is concluded that large clearance has lower friction factor than small clearance, and full fluid film lubrication is unlikely to have developed between the MOM bearings in this study, even with a small clearance and high viscosity

There is currently much interest in the wear of metal-on-metal THRs and potential concerns about elevated metal ion levels. Generally, wear of metal-on-metal THR’s has been low in simulator studies. Slightly higher and more variable wear has been found clinically. Variations in surgical approach, technique and fixation method may influence the level of force applied across the prosthesis during gait. It is hypothesised that increased joint tensioning may increase loading of THR’s during the swing-phase; leading to elevated wear and friction due to depleted fluid film lubrication. This study aimed to assess the effect of swing-phase load on the friction, lubrication and wear of metal-on-metal THR’s. Cobalt-chrome 28mm metal-on-metal THR’s were tested in a physiological hip simulator, loading was modified to provide; (1) ISO swing-phase load (280N, as per ISO 14242-1) and (2) low swing-phase load (< 100N). Friction testing was conducted using a pendulum friction simulator, with 280N and 100N swing-phase loads. Theoretical lubrication modelling was carried out using elastohydrodynamic lubrication theory. The overall mean volumetric wear rates was 10-times greater in THR’s tested with an ISO swing-phase load in comparison to THR’s tested with low swing-phase loads (0.58±0.49 compared to 0.06±0.039mm. 3. /million cycles). The friction factors were 0.129 and 0.173 respectively under low and ISO swing-phase conditions. A decrease in the predicted lubricant film thickness when the swing-phase load was increased was observed; at the start of stance phase this was 0.12microns and 0.07microns under low and ISO swing-phase conditions respectively. The results demonstrate that the performance of metal-on-metal THR’s is highly dependent on swing-phase load conditions. It is postulated that fixation method and surgical technique can affect the swing-phase load. This study has demonstrated that over-tensioning of the tissues may also accelerate wear. These observations may explain some of the variations reported clinically

Background: This study was undertaken to investigate the differences in the metal ion serum concentrations after implantation of a MetaSUL-THR and a Birmingham Hip Resurfacing in comparison to implant free subjects and to review the influence of factors, possibly influencing the wear behaviour of the articulation. Methods: Serum levels of cobalt, chromium and molybdenum in 74 patients after primary implantation of a MetaSUL-THR and in 111 patients after BHR were compared with the levels found in 130 control subjects without implants. Serum ion concentration was determined by atomic absorption spectrophotometry. Furthermore, the correlation between serum ion concentration and in-situ time, implant size and cup inclination was studied. Results: The chromium and cobalt concentrations of BHR-patients as well as the chromium concentration of bilateral MetaSUL-THR-patients, however, were significantly higher as the concentrations of patients with unilateral MetaSUL-THR and the control group. The molybdenum serum concentration was very similar in all investigated groups. The chromium serum concentration in patients with unilateral MetaSUL-THR and in patients with BHR showed the highest level in the postoperative period from 7 to 12 months. Analyses of the subgroups showed an association between higher cobalt serum levels and cup inclination greater than 50 in patients with unilateral MetaSUL-THR more than 12 months after implantation. A statistically significant negative correlation was detectable between implant size and chromium as well as cobalt serum concentration in BHR-patients studied more than 12 months after implantation. Conclusions: Metal-on-metal bearings of large diameter result in a greater systemic exposure of cobalt, chromium and molybdenum ions than bearings of smaller diameter. It is not known to what extent the different levels are due to corrosion of the surfaces of the components or to the amount of wear particles produced. The chromium concentrations were highest 7–12 months after operation, what may due to a running-in of the bearing like known from hip simulator studies. Interestingly implant size and metal ion serum levels correlate negatively in the BHR-patients studied more than 12 months after implantation. That could be due to an existing fluid film lubrication in these bearings and may be caused by the thicker fluid film in bearings with greater radius

Purpose: Articular surface replacement (ASR) is an alternative for young patients considered for hip replacement. The in vivo release of ions from these surfaces has yet to be well evaluated. The purpose of the present study was to compare the concentrations of metal ions in blood of patients with ASR and metal-on-metal (MM) total hip arthroplasty (THA). Methods: Blood was collected 6 months after implantation time into Sarstedt Monovette® tubes for trace metal analysis from patients having ASR (n=61), 28 mm-head MM THA (n=18), and 36 mm-head MM THA (n=25). The concentrations of cobalt (Co), chromium (Cr), and molybdenum (Mo) were analyzed by inductively coupled plasma-mass spectroscopy (ICP-MS). Results: The median Co level was not significantly different between the 3 groups (2.35 ppb, 2.00 ppb, and 2.50 ppb for the 28 mm MM THA, 36 mm MM THA, and the ASR patients, respectively). The median Cr level was significantly lower in the 36 mm MM THA patients (0.10 ppb) compared to the 28 mm MM THA (0.15 ppb) and the ASR (0.40 ppb) patients. The median Mo level was significantly lower in the 36 mm MM THA patients (1.30 ppb) compared to the 28 mm MM THA (2.00 ppb) and the ASR (1.50 ppb) patients. Conclusions: Our results show that the level of ions in 36 mm MM THA patients was lower than in 28 mm MM THA patients. This can be explained by the fact that 28 mm MM bearings are resistant to microseparation during the normal gait cycle, which is theoretically accompanied by a reduction of fluid film lubrication and increased potential for the production of wear debris. Our results also show that the ion levels in patients having ASRs is similar to that observed in 28 mm MM THA patients but higher than in 36 mm MM THA patients. The diametric clearance of ASRs is typically much greater and the potential for a ‘suction fit’ may be less, leading to higher ion production. The concentration of ions in long-term follow-up remains however to be elucidated. Funding: Educational Grant from the Canadian Orthopaedic Foundation

Introduction: Pseudotumours (soft-tissue masses relating to the hip joint) following metal-on-metal hip resurfacing arthroplasty (MoMHRA) have been associated with elevated serum and hip aspirate metal ion levels, suggesting that pseudotumours occur when there is increased wear. This study aimed to quantify in vivo wear of implants revised for pseudotumours and a control group of implants revised for other reasons of failure. Methods: A total of 30 contemporary MoMHRA implants in two groups were investigated in this Institutional Review Board approved study:. 8 MoMHRA implants revised due to pseudotumour;. 22 MoMHRA implants revised due to other reasons of failure (femoral neck fracture and infection). The linear wear of retrieved implants was measured using a Taylor-Hobson Roundness machine. The average linear wear rate was defined as the maximum linear wear depth divided by the duration of the implant in vivo. Results: In comparison with the non-pseudotumour implant group, the pseudotumour implant group was associated with:. significantly higher median linear wear rate of the femoral component: 8.1um/year (range 2.75–25.4um/year) vs. 1.79um/year (range 0.82–4.15um/year), p=0.002; and. significantly higher median linear wear rate of the acetabular component: 7.36um/year (range1.61–24.9um/year) vs. 1.28um/year (range 0.18–3.33um/year), p=0.001. Similarly, differences were also measured in absolute wear values. The median absolute linear wear was significantly higher in the pseudotumour implant group:. 21.05um (range 2.74–164.80um) vs. 4.44um (range 1.50–8.80um) for the femoral component, p=0.005; and. 14.87um (range 1.93–161.68um) vs. 2.51um (range 0.23–6.04um) for the acetabular component, p=0.008. Wear on the acetabular cup components in the pseudotumour group always involved the edge, indicating edge-loading of the bearing. In contrast, edge-loading was observed in only one acetabular component in the non-pseudotumour group of implants. The deepest wear was observed well within the bearing surface for the rest of the non-pseudotumour group. The difference in the incidence of edge-loading between the two groups was statistically significant (Fisher’s exact test, p=0.03). Discussion: Significantly greater linear wear rates of the MoMHRA implants revised due to pseudotumour support the in vivo elevated metal ion concentrations in patients with pseudotumours. This study provides the first direct evidence to confirm that pseudotumour is associated with increased wear at the MoM articulation. Furthermore, edge-loading with the loss of fluid film lubrication may be the dominant wear generation mechanism in patients with pseudotumour

Introduction: A renewal of interest in large metal-on-metal bearings has been seen due to the introduction of resurfacing prostheses. According to lubrication theory, large metal-on-metal bearings may obtain a film fluid lubrication. The mode of lubrication may be described by the lambda coefficient λ, which is the ratio between the thickness of the lubricant hc and the root mean square roughness of the bearing Rq. If this coefficient λ is higher than 3, a fluid film lubrication is expected. To have this situation, the following parameters must be optimized: diametral clearance and roughness. This presentation investigates the role of these two parameters, based on two commercially available products. Methods: To determine the λ coefficient, the thickness hc of the lubricant must be determined, as well as the roughness of the bearing Rq. The Hamrock – Dawson equation (. 1. ) allows the determination of the thickness hc as a function of the bearing parameters. The roughness Rq is measured by a stylus profilometer. Results: With a typical load of 3000 N, an angular velocity of 1 rad/s, and a viscosity of 0.005 Pas, the Hamrock – Dawson equation gives the following film thickness hc for a 50 mm metal-on-metal bearing with different diametral clearances:. Diametral clearance [μm] 100 150 200 250 300< . Minimum thickness hc [nm] 64.9 47.5 38.1 32.1 27.9. The following roughnesses Rq were measured for two types of resurfacing prosthesis:. As cast CoCr alloy (BHR by MMT): 23 ± 6 nm. Wrought-forged CoCr alloy (DUROM by Zimmer): 5 ± 2 nmThe as cast resurfacing prosthesis has a 250 μm diametral clearance and the wrought-forged resurfacing prosthesis has a 150 μm diametral clearance. Therefore, the following λ coefficients for a 50 mm metal-on-metal bearing are obtained:. As cast CoCr alloy: 0.99. Wrought-forged CoCr alloy: 6.72. This large difference in the λ coefficients indicates that the lubrication mode of these two different prostheses is probably different. Based on this analysis, the wrought-forged component has ideal lubrication (λ > 3) whereas the as cast does not reach ideal lubrication (λ < 3). Conclusions: This investigation shows that minute differences in the geometry and in the roughness of a metal-on-metal prosthesis may significantly influence their lubrication behaviour as well as the wear resistance