Adverse Wear in MOM Hip-Arthroplasty Related to the Production of Metal Fragments at Impingement Sites

Metal on metal (MOM) bearings were reintroduced as resurfacing arthroplasty (RA) for the younger, more active patient and were later incorporated into total hip arthroplasty (THA). Early results were encouraging. However, recent publications identified adverse tissue responses to metal debris, such that the majority of MOM designs have been abandoned due to the increase in cobalt-chromium (CoCr) debris and associated metal ions. Reports of MOM THA cited risks that included acetabular cups with high-inclination angles, i.e. “edge-loading”, and “trunnionosis”. Hip impingement was also a cited risk in one MOM study, with “type-IV” wear noted to be a sliding/impaction type of wear, characterized by deep scratches. Sliding/impaction wear mechanisms produced at impingement are not well represented in current MOM literature. Therefore, our objective in this review was to consolidate evidence for impingement risks. We hypothesize that hip impingement and subluxation with metal-backed acetabular cups can trigger wear mechanisms that result in, 1) femoral-neck notching, 2) release of large metal particles, 3) production of uniquely large scratches, defined as “microgrooves” on heads and cups, 4) formation of “polar” and “basal” microgrooves precisely aligning with cup profiles during impingement, and 5) equatorial microgrooves relate to soft-tissue sites of impingement. Relevant risk scenarios were evaluated and included hip impingement in both sitting and standing postures, head subluxation, wear patterns defining in-vivo component positions, and evidence for circulating metal fragments. The study relied on mapping of wear patterns to deduce in-vivo positioning of devices and relied on surrogate femoral stems of the same brand to simulate neck-cup impingement. EOS imaging techniques were used to analyze functional-sitting and functional-standing postures and prove existence of hip impingement sites in patients. The study identified 8-risk scenarios for wear damage on MOM bearings. The microgrooves on femoral-heads crossing the main-wear area (polar) and non-wear regions (basal) aligned well with cuprim profiles at impingement sites. This may represent the first description of such large scratches (40 - 300 μm wide) we termed microgrooves, that formed on femoral heads at sites representative of prosthetic impingement. As an abrasive wear process, similar to the formation of femoral-neck notches, these would have been acquired over millions of gait cycles. The pitting and linear microgrooves crossing the non-wear areas of heads (basal) represented the ingress sites of circulating metal particles. Similar micro-grooves were evident in acetabular cups, also signifying 3rd-body abrasion by large metal particles. Hip impingement and head subluxation were implicated by the unequivocal evidence of 3rd-body abrasive wear as the triggering events producing large metal fragments. One caveat regarding retrieval studies is that such damage may be only representative of failed MOM devices. This study demonstrated that emerging technologies such as EOSTM x-ray analyses can reveal subtle changes in implant positioning using patient shifts in functional postures (sitting, standing, hyper-extension, etc.), and thereby assess impingement/subluxation risks in the clinical setting before failure occurs.

Hip impingement was also cited as a common risk with McKee-Farrar type THA [39] [40] [41].Howie et al. (2005) were able to determine component positioning in-vivo because the femoral stems were of monobloc design.They noted that cup-to-neck impingement sites demonstrated fatigue damage from sub-surface fractures, resulting in extrusion of large metal fragments.This was believed to represent a sliding/impaction type of wear mechanism.Such femoral-neck/stem impingement with acetabular cups was not surprising because the THA literature is replete with documentation of dislocations, liner impingements, rim fractures, ceramic chipping, neck notching, component disassociation and related black-staining of ceramic bearings [42]- [48].Prevalence of THA impingement in retrieval studies has varied from 39% to 83% of cases [49] [50] [51] [52] [53].The McKee-Farrar study also provided microscopic details of CoCr wear patterns.Four types were described; Type I-II wear patterns contained a background of randomly-oriented, fine scratches, with CoCr surfaces retaining their original reflective appearance.We would also note as typical strings of exposed carbides 5 -10 µmin size (Figure 1).Type III wear patterns had randomly-oriented scratches with a higher roughness that resulted in loss of reflective surface (Figure 1(B)).In contrast, type IV wear was characterized by deep, parallel scratches that created a 10-fold higher roughness due to scratches typically 40 -100 µm wide with linearly-striated side-walls (Figure 1 Using white-light interferometry (WLI) we confirmed the presence of dramatically long scratches typically 100 µm wide and 2 -4 µm deep (Figure 2) [40] [54] [55].These we termed "microgrooves" (Figure 1(C)) to uniquely distinguish them from the fine, background scratches on CoCr surfaces (Figure 1(A), Fig- ) and the "stripe wear" defects reported in ceramic retrievals [51] [56] [57].
In our THA study [54], pitting and microgrooves were detectable on all retrieved components (Figure 1), being more than 10-fold larger than typical background CoCr scratches and carbides.Microgrooves were identifiable by extreme lengths, raised lips and ranging 40 -160 µm with conspicuous longitudinal striations (Figure 1(C), Figure 2).These appeared very similar to type-IV scratches reported in the McKee-Farrar study (Figure 1(D)) [40].Our assumption was that 100 µm wide scratches had been created by CoCr particles 100 µm or larger.However, we found no evidence to support the presence of large CoCr fragments.It is therefore significant that 96% of particles found embedded in the plastic liners of metal-on-polyethylene (MPE) retrievals were metallic, averaging 126 µm in size (ECD: equivalent circle diameter), and some even larger than 2.5  mm [46] [58].The conceptual sliding/impaction/fatigue wear mechanisms that were described relative to THA impingement [40] are not represented in current literature espousing the risks of "steep-cups" and "trunnion corrosion".Therefore, the objective of this study was to consolidate the available evidence for impingement/wear mechanisms, and to determine from this assemblage of information (Table 1), was this could be a clinically relevant risk scenario, or should it be rejected.
We formulated the following hypothesizes: 1) THA impingement can readily occur in either sitting or standing postures.
2) Neck notching is an impingement/abrasion process produced by the cup-rim over millions of cyclic hip motions.
3) Hip impingement and femoral-head subluxation release metal fragments into the joint space.
4) Ingress of metal particles into MOM bearings produces 3 rd -body wear damage most evident in "non-wear" (basal) regions of femoral heads.

Hip Subluxation in Functional Standing and Sitting Postures
It is known that cup positions change depending on patient position (Figure 3).
During sitting, the pelvis generally tilts posteriorly and both cup anteversion and inclination increase (Figure 4).Assessment of patient's lateral or supine position during surgery does not eliminate the risk of impingement and subluxation,   even if cup position is representative of the so-called "safe zone" [59].The high rate of THA impingement [15] [22] [31] [45] [49] together with the fact that dislocation can occur when the cup is placed in the "safe zone" has demonstrat-ed that hip impingement, subluxation and even dislocation can occur due to functional postural changes.The trial reduction intraoperatively cannot determine impingement risks in the patient's various functional postures.Moreover, the spino-pelvic mobility of each patient makes the functional position of the cup complex.[60] Patients with pelvic stiffness have less change in anteversion and inclination with sitting, i.e. the cup should be implanted in more inclination/anteversion to improve motion.The opposite is true in patients with a hypermobile pelvis, usually women.The cup needs to be placed in less inclination/anteversion because with sitting there will be larger than normal shifts in cup inclination/anteversion while risk of impingement or even dislocation increases [61].In addition, the balance of the spine in the sagittal plane requires attention.Patients with unbalanced spines should 1) have sagittal deformity corrected before proceeding to THA, or 2) have cup placed in less anteversion because of the risk of posterior impingement with a retroverted pelvis and increased acetabular anteversion [62].

Wear Patterns Defining In-Vivo Component Positions
The key measure in retrieval analyses lies in discerning the in-vivo orientation of components.The prior study of McKee-Farrar THA had the advantage that the femoral components represented a monoblock design [40].To determine in-vivo positioning of modular bearings, we utilized wear-pattern mapping developed from simulator studies [21] [63] [64].This unique approach defined component wear-patterns using a combination of light microscopy, white light interferometry (WLI: NewView-600, ZygoInc, Tucson, AZ), and scanning electron microscopy (SEM: MA-15: Zeiss Inc., New York).Wear patterns on the retrieved components were stained red to illustrate main-wear zones for photography (Figure 5: MWZ, area of habitual wear) and also to delineate non-wear zones (Figure 5 NWZ: region of incidental, non-wear) [54].This was necessary for photography because the retrieved CoCr bearings retained their original, highly-reflective appearance.In addition, cup surfaces had to be taped to eliminate multiple images reflected from convex surfaces (see Figure 24) [21] [54].Femoral heads were photographed in four orthogonal views and one polar view whereas cups were simply photographed en-face.Positioning of the narrow NWZ-margin (Figure 5(A), B: S) defined the superior aspect of the femoral head and position of the habitual wear area (MWZ) in vivo.This we validated on THA received with heads fused to their femoral trunnions (Figure 6).To define the cup's in-vivo position, the typically eccentric position of its MWZ area was matched to that of the femoral MWZ.The sites of microgrooves visible to the naked eye on head and cup components were colored for photography (Figure 5, Figure 6: polar as blue, equatorial as green, basal as black).

Notching Mechanism in Femoral Necks
Howie et al. [40] noted that "femoral-neck on cup rim" impingement resulted in a fatigue-wear mechanism capable of releasing large CoCr particles.While the  [66]- [71].There was no opportunity to check for circumferential neck-markings indicative of cup impingement because the majority of our MOM bearings were retrieved without mating femoral stems (Figures 7-9).While some cases could be related to multiple dislocations [66].the anatomy of these notches indicated an abrasive and/or fatigue-wear phenomena that occurred repetitively over millions of impingements (Figure 7).For example, the titanium femoral neck in   our SROM case (Figure 7(C)) had two notches that exactly matched the rim profiles of the Pinnacle shell and CoCr liner [71].This resembled a precision-machining process, unequivocal retrieval evidence that such neck-notching required millions of wear cycles to acquire.Some femoral necks demonstrated two and sometimes three notches (Figure 7(A)).Using geometric THA models, [43] we have shown that the proximal notch indicated the 1 st impingement site (Figure 7(A)).For the more distal notch, the femoral head had to sublux to a more vertical position, relative to the polar axis (Figure 8(B), Figure 8(D)).Such a mechanism, whereby the femoral neck was worn by repetitive oscillations of the cup rim, we defined by the acronym "NAR-damage" (Table 2).This was variable, from cosmetic scratches more typical on CoCr necks (Figure 7(A)) to deep notches found onTi6Al4V necks (Figure 7(B), Figure 7(C)).In this regard, it is notable that the majority of mating CoCr cups showed no comparable rim damage.
There are many factors involved in THA impingement and certainly head: neck ratios and range of motion are important with many retrieval studies featuring 28 mm THA (Figure 7).Nevertheless, THA designs optimized for range of motion can also impinge and produce neck notches (Figure 9).

Pits, Microgrooves and Plastically-Deformed Gouges
There was unequivocal evidence of large pits in all retrieved MOM bearings (Figure 10(A)).The basal head areas (non-wear zone) in particular provided the most dramatic evidence.This was likely because basal regions represent the first sites of ingress for circulating metal particles [49] [58] and such damage was not mitigated by habitual wear during patient's normal activities (Figure 5, Figure 6: non-wear zone).Strings of surface pits were characterized by 100 -300 µm width, smooth entry points, longitudinal striations indicating direction of travel, and lips raised towards the point of egress (Figure 10(B)).WLI imaging showed that pits typically varied 3 -10 µm in depth (Figure 11, Figure 12).The pits presented partly as a ploughing action that raised scratch lips above the surface (plastic deformation) and partly abrasive action (releasing CoCr debris).For    discussion purposes, pits will be defined as a 3 rd -body abrasive-wear mechanism, using acronym "3CO-damage" as the descriptor.However, it is to be noted that we were unable to find any evidence of CoCr fragments or CoCr smears representing transfer onto bearing surfaces.
All retrieved MOM bearings revealed microgrooves from 40 to over 100 µm wide with raised lips and linearly-striated sidewalls (Figure 13) [54].Depending on location, these were defined as basal, polar or equatorial microgrooves (Figure 5).Our retrieval study may be the 1 st to confirm such "type IV" wear as described in the McKee-Farrar study [40].In addition, the microgroove characteristics, i.e. 100 µm width, longitudinal striations, and plastically-deformed lips (Figure 13, Figure 14) appeared very similar to the large pits (Figure 10, Figure 11) and both will also be considered representative of 3 rd -body abrasive wear by large CoCr particles (Table 2: 3CO).
Surface "gouges" were described in a retrieval study of large diameter MOM.
Gouges ranged up to 1.5 mm length, 25 -75 µm width, and 0.25 -1 µm depth [74].These were observed on the majority of retrievals and lacked longitudinal striations typical of microgrooves.The authors attributed the gouges on heads to impaction by the cup rims, i.e. a plastic deformation mechanism [74].Our SEM analysis revealed similar arrays of parallel gouges and surrounding slip bands (Figure 15).These were shallow depressions 1 -3 mm long, showing extensive plastic flow onto surrounding surfaces (Figure 16).For discussion purposes, we shall term femoral-head gouging by the acronym "FHG-damage".

Cup Positions Defining Femoral-Neck Impingements
Our study of modular MOM retrievals may be unique in that head and cup  wear-patterns were mapped to discern how each component was positioned in vivo (Figure 5, Figure 6) [54].In consequence, it was possible to map the locations of microgrooves with reference to likely neck-on-cup impingement sites (Figure 8, Figure 9).Polar microgrooves crossed the main-wear zone (Figure 5:  In contrast, equatorial microgrooves tended to align in the transition zone around MWZ-boundaries, their orientation being conspicuously different from basal and polar types.A commonality for all microgrooves was scratch-widths that could span hundreds of microns with raised lips and conspicuous longitudinal striations of sidewalls (Figures 10-14).
The majority of our modular THA bearings were retrieved without mating femoral stems.We therefore used femoral-stem surrogates from inventory when studying likely angles of cup-impingement (Figure 8(C)).The major finding in impingement simulations was that rim-profiles of cups overlaid the basal and polar microgrooves marked on RA and THA heads (Figure 8(C), Figure 8(D), Figure 17).The microgrooves were not always continuous, sometimes obscured by alayer of protein contaminants [63].Nevertheless, there was generally enough evidence of multiple scratches tracking from base of head into the polar regions of main-wear zone (Figure 6).Some retrievals demonstrated several basal-polarpairings, indicative of multiple impingement sites (Figure 17) [73].It was noted that equatorial microgrooves around the main-wear zone boundaries were less predictable, could vary from short to considerable length, and were generally not at locations associated with prosthetic impingement (Figure 18).
Our comparisons of both THA and RA femoral components showed essentially similar patterns of microgrooves.The natural bony necks retained with RA femoral shells reduced head: neck ratios and limited the available range of motion [75].Our microgroove evidence in RA cases revealed that patients routinely compensated by head subluxation [55].The quandary was in deducing what abrasive wear mechanism formed such large microgrooves in RA and THA bearings?Was it the cup rim or the entrained metal particles?The former would represent Mode-2 wear as described by McKellop et al. [76] and the latter would represent Mode-3.For discussion purposes, microgrooves produced by the cup rim or entrained metal debris will be differentiated by the acronyms 2CR-damage and 3CR-damage (Table 2).

Evidence of Metal Debris Circulating in the Hip Joint
SEM analysis demonstrated basal scratches that resembled 100 µm wide microgrooves, except they lacked typical longitudinal striations (Figure 19).WLI imaging frequently revealed multiple parallel tracks that represented metal transfer of 1µm thickness with 3 -5 µm peak heights (Figure 20).SEM analysis (Figure 21(A)) and energy dispersive spectroscopy imaging revealed predominantly elemental titanium (Ti) tracking along CoCr surfaces (Figure 21).SEM analysis also revealed longitudinal surface striations exiting some transfer layers.These tracks were therefore considered microgrooves coated by a layer of titanium transfer.Clinical studies of MOM THA have demonstrated that high concentrations of Ti-ions correlated with femoral-neck notching noted in revised Ti6Al4V stems [77].This unequivocal evidence of metal transfer proved existence of large  or CoCr-transfer.The quandary here was in deducing did the Ti6Al4V particles actually damage the CoCr surface i.e. created microgrooves, or did they just form a transfer layer that coated pre-existing microgrooves?For discussion purposes, microgrooves produced by abrading Ti6Al4V particles will be termed 3TI-damage and titanium transfer will be termed TTL-damage (Table 2).

EOS Demonstration of Spino-Pelvic/Hip Motions at Impingement Sites
EOS imaging with 3D-reconstructions in standing and sitting positions provided details of cup functional inclination and anteversion.Knowing femoral anteversion, the important combined anteversion could be determined.EOS images in the functional-standing position of our 1 st example show a cup with 40˚ inclination but excessive 48˚ anteversion (Figure 22(A)).With 34˚ of femoral anteversion, this hip demonstrated 82˚ combined-anteversion. Shifting from functional-standing posture (Figure 22(B-1)) into hyperextension (Figure 22(B-2)) determined available range of motion.The cup impingement site was demonstrated by 3D-reconstruction (Figure 22(C)).This patient's 15˚ extension ability in functional-standing position proved insufficient (Figure 22(D)) and patient could sense anterior subluxation of the head approaching within 5˚ of impingement site (Figure 22(B-2)).However, in functional-sitting posture, the pelvic tilt increased slightly to 25˚ thereby providing a 5˚ increase in cup anteversion.With 58˚ cup inclination in sitting posture, this hip had 63˚ of motion before impingement.Thus, EOS imaging demonstrated no limitation in functional-sitting.EOS images in the functional-standing position ofthe2 nd example showed a cup with 40˚ inclination and 35˚ anteversion (Figure 23(A)).Including 15˚ of femoral anteversion, this hip demonstrated 50˚ of combined anteversion.This patient's standing posture showed 37˚ motion available before neck-on-cup posterior impingement for extension testing.Thus, EOS imaging demonstrated no significant limitation in functional-standing.However, in functional-sitting position (Figure 23

Discussion of MOM Wear Concepts
As part of our analysis of large diameter MOM retrievals, we defined eight potential types of damage (Table 2).The unequivocal evidence of circumferentially-notched femoral-necks (Figures 7-9) represented, 1) NAR-damage (Table 2) that could only have occurred over millions of gait cycles, and 2) notches that unequivocally defined sites of prosthetic-impingement (Figure 8(C), Figure 9).We recognize that a loose and migrating metal cup could also produce damage in failing hip-procedures.However, it would be difficult to conceive that loose cups, patients suffering from multiple dislocations [71], or even inadvertent damage during surgery, could produce such neck notching.Thus, our conclusion was that neck notches represented abrasion by the cup rim, an unintended consequence representative of 2-body abrasion, thus confirming our 2 nd hypothesis.
Impingement has been a frequently-raised concern in McKee-Farrar studies [28] [39] [40] [41] [78].Our current focus on impingement in modular MOM bearings was based on wear analysis of the "fixed-head" McKee-Farrar design [40].Howie et al. described "impingement marks" in nine of 29 THA and noted extrusion of metal fragments due to sub-surface fatigue.However, in our opinion, their landmark finding lay in the description of "type-IV" wear patterns.
These were described as deep and parallel wear tracks that spanned approx-imately 100 µm width on highly-reflective head surfaces.Ours may be the first to confirm this type-IV wear evidence.We found ample evidence of 100 µm wide scratches (and larger) and similar sized pitting.We termed these type-IV scratches as "microgrooves".The microgrooves were significantly larger than anything described in current MOM literature and dwarfed the scale of exposed carbide formations frequently attributed to scratch formations (Figure 1, Figure 10, Figure 13, Figure 21(A)) [28] [78].Microgroove characteristics included long curvilinear tracks, raised lips (evidence of plastic deformation), and longitudinal striations (evidence of ploughing/abrasion).Salient observations made from this review of microgroove formations included; 1) Curvilinear microgrooves crossing the main-wear zones in polar areas of femoral heads had to be forming repeatedly, otherwise they would have been eradicated by the hip's normal and routine wear process.
2) Neck-on-cup prosthetic impingement (NAR-damage) appeared to be the sole mechanism that could produce observed consistency in siting of basal/polar microgrooves.This was supportive of hypothesis-5.
3) The variability of equatorial microgrooves around the periphery of main-wear zones was not related to prosthetic-impingement sites.Most likely these microgrooves represented impingement with soft-tissues, a possible confirmation of hypothesis-6.
4) The large pits and linear microgrooves crossing basal head areas appeared an enigma, since these were designated "non-wear" regions.However, as others have described, these areas would represent the ingress sites of circulating metal particles [46] [79].As noted, these were not areas of normal head-wear and therefore basal surfaces were well preserved, confirminghypothesis-4. 5) Cup microgrooves could only have been formed by circulating metal particles, and therefore represented 3 rd -body abrasive wear, confirminghypothesis-8.
6) The circular shape of femoral wear-patterns (Figure 6) was not duplicated in cups.The cup wear-patterns were mostly eccentrically positioned around arcs of cup rim (Figure 24).7) Large arcs of cup wear represent "edge-loading" may be representative of head subluxation or sub-optimal cup positioning.What we did not find was any evidence of tracks that would have represented transfer of CoCr debris.We had to infer the existence of CoCr particles from pit and scratch morphologies (Figure 2, Figures 10-12, Figure 14) that revealed raised lips (plastic-deformation) and linear striations (abrasion).These features represented the classic signature of 3 rd body abrasion by hard particles.Nevertheless, our SEM/EDS analyses did confirm layers of Ti6Al4V contamination smeared over similar-sized microgrooves (Table 2: TTL damage).Titanium transfer onto head microgrooves was also commented on in a previous SEM study (see Band et al.,figs. 6.38,6.39)[80].These authors speculated that Ti-transfer could have originated from debris released from ingrowth-surfaces.
However, in THA devices with Ti6Al4V-shells or Ti6Al4V-stems, titanium particles could equally originate from prosthetic impingement (Figure 7, Figure 8).The Ti-ion concentrations detected in vivo [81] and titanium smears on CoCr retrievals represented unequivocal evidence of 1) prosthetic impingement onTi6Al4V components, 2) release of Ti6Al4V particles, 3) ingress of circulating Ti6Al4V particles into MOM bearings, thereby forming 4) Ti6Al4V transfer layers that resembled microgrooves.We demonstrated in the laboratory setting that introduction of both Ti6Al4V and CoCr particles produced microgrooves in CoCr surfaces (Table 2: 3CO, 3TI) and provoked adverse wear in simulator tests [82] [83].This accumulation of evidence therefore is supportive of our 3rd hypothesis that hip impingement and head subluxation represent major risks for release of large metal fragments.
The unique finding in our simulated "femoral-neck/cup-rim" impingements was that cup rims invariably followed tracks of basal and polar microgrooves (Figure 8(C), Figure 17, Figure 18), confirming hypothesis-5.Two possibilities were that, 1) cyclic loading by the cup rim produced plastic deformation represented by gouge defects (Table 2: FHG-damage) [74] or 2) cyclic abrasive motion produced microgrooves (Table 2: 2CR-damage).It was equally possible that circulating metal fragments trapped under the cup rim moved with it, their ploughing action producing microgrooves (Table 2: 3CR-damage).The similar morphology of large pits (Figures 10-12) and microgrooves (Figure 13 2: 3CR).This was supported by evidence of cup microgrooves, wherein the only possibility was abrasion by circulating metal particles.Also compelling in an unrelated study was retrieval evidence of metal particles (126 µm avg.size) embedded in polyethylene cup surfaces [58].
Such correlations appeared very supportive of a3 rd -body wear hypothesis.Nevertheless, the evidence of microgrooves of considerable length aligned with cup-rim profiles was also suggestive of 2-body abrasion ( There was ample evidence of plastic-deformation in modular CoCr bearings. The raised side-walls of microgrooves and the presence of slip bands on scratch shoulders attested to plastic-flow in damaged CoCr surfaces.Intersections of crossing microgrooves provided further evidence of cold-flow (Figure 14).
Larger gouges surrounded by arrays of slip bands represented evidence of plastically-deformed defects [74].These we also found and could be attributable to indents made by an impinging cup rim ( bearings have a soft surface that can readily absorb 3 rd -body debris including large metal particles [49] [84].Thus, the accumulating evidence is persuasive that it is the production of large metal fragments that triggers adverse wear.This we would consider proof that, unlike more forgiving MPE bearings, MOM bearings are extremely sensitive to the ingress of metal debris. The limitations of this study are common to other retrieval studies.Components were seldom received with any markings to indicate position at revision surgery.Thus, we relied on mapping of wear-patterns to deduce in-vivo positioning.Retrieval of femoral stems proved to be an infrequent occurrence in these 2 nd generation MOM designs.Hence, we lacked evidence of femoral impingement.We also had to rely on surrogate femoral stems of the same brand for neck-cup impingement studies such that the equivalent size neck/femoral stem would simulate the original device.In addition, these data relate only to failed MOM bearings.The visual and microscopic evidence of large pits and polar microgrooves persisting in habitual wear patterns (main-wear zones) denoted repetitive and consistent episodes of hip impingement and subluxation in these retrievals.However, we have no knowledge of whether such wear mechanisms either contributed directly to the failures, or would be present in more successful cases.
Hip impingement and subluxation of the femoral head are key concepts in understanding "normal" functioning of THA and predicting the risk of adverse conditions.In the activities of daily living, patients are continually implementing a succession of standing and sitting postures.The roles of 1) hyperextension, and 2) combined flexion and rotation, reflect the importance and recognition of "critical contact zones" occurring between femoral neck and rim of the acetabular cup.Our EOS studies showed that THA impingement and head subluxation can be demonstrated in patient's functional postures, notably standing, full extension and sitting, and can be present even when the cup is positioned in the "safe zone".[60] [89] EOS results confirmed our 1 st hypothesis and this was regardless of whether THA designs had 28 mm heads (Figure 8(C)) or larger (Figure 9).These EOS observations supporting the analysis of retrieved MOM bearings can now be carried into clinical studies of THA devices to discern which patients have normal function and which risk impingement, subluxation and dislocation.

Conclusion
By consolidating the impingement/wear evidence from retrieved MOM bearings, 8-risk scenarios were identified.Neck/cup impingement has been confirmed by 1) circumferential scratches and notches on femoral stems, and 2) microgrooves dominating specific locations on femoral heads.In basal and polar regions of the femoral head, these represented sites of prosthetic impingement.Open Journal of Orthopedics In equatorial regions of the femoral head, we hypothesize that these represented impingement sites with soft-tissues.This retrieval evidence demonstrates that the rim of an impinging CoCr cup can result in abrasive damage on the femoral head (2CR: 2-body wear; 3CR, 3 rd -body wear) as well as femoral-neck notching (Table 2: NAR, 3 rd body wear).In this regard, we were surprised to find that such self-evident impingement damage on MOM bearings, as first described by Howie et al. [40] apparently has received no attention over the past 13 years.
This applies to some metal-backed polyethylene cups (Figure 9) as well as CoCr cup designs.It is noted that metal-backed cup designs offer the surgeon many options.Nevertheless, the National Joint Registries have shown that cemented polyethylene cups have consistently better clinical outcomes than non-cemented cups, i.e. the metal-backed cups have not been as forgiving [26] [90].EOS imaging and associated 3D-reconstructions will also aid our understanding of the retrieval data and better conceptualizing of optimal component positioning in patients with differing complexities of spino-pelvic mobility.In turn, EOS imaging of implant positioning in the clinical setting will offer an improved diagnosis with respect to patient's functional postures and help determine risk of failure.

Figure 2 .
Figure 2. White light interferometer (WLI) images: fine scratches adjacent to large pit: (A) View of scratch (1) and profile trace (xx) crossing pit; (B) Cross-section of pit (xx) as traced in image-A; (C) Light-microscopy image (in image-A); (D) 3D-oblique view: raised lips around scratch and pit.

6 ) 7 )
Cups positioned along equatorial microgrooves do not represent sites of 'simulated' prosthetic impingement.Head microgrooves are produced by abrasion over millions of cyclic hip motions due to a combination of, a) cup-rim cycling across head surface (2-body wear), and b) motion of entrapped metal particles (3 rd -body wear).

Figure 9 .
Figure 9. Metal-on-polyethylene THA with neck notch at impingement site.

Figure 19 .
Figure 19.SEM image of twin 100 µm microgrooves extending from base of head in polar direction (47 mm ASR XL).Metal transfer (arrows) shown obscuring any longitudinal striations.

Figure 24 .
Figure 24.Position of main-wear zone (MWZ) representative of superior quadrant in retrieved cup (46.5 mm ASR).Cup rim-wear produced by subluxing head extends around large arc (213˚) while femoral neck rotated against contra-rim (neck arc).

Table 2 .
Wear damage observed on retrieved MOM bearings.

Table 2 :
[84] or damage produced during revision surgery (Table2: 2OR).Either way, we were not impressed that these were as common or consistently present as the 100 µm microgroove formations.Therefore, we support ouroverriding 3 rd -body wear scenario, that impingement and head subluxation trigger the release of metal fragments.These metal particles will readily circulate in the hip during patient gait and ingress between moving bearings[46][49][84].There is also the added risk with highly-inclined and highly-anteverted cups.Such patients are likely to have more frequent and more adverse THA impingement episodes than normal.
[85]concept of hip impingement occurring without the patient's awareness we termed a repetitive sub-clinical subluxation (RSS) phenomenon[73][85].An appropriately-positioned acetabular cup will reduce the risk of the metal acetabular shell impinging on a metal femoral-neck (Table2: NAR-damage).However, with hip impingement and subluxation there remains the risk of the fe-