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Symposium: Papers Presented at the Annual Meetings of The Hip Society

Ceramic Bearings for Total Hip Arthroplasty Have High Survivorship at 10 Years

D’Antonio, James A. MD1, a; Capello, William N. MD2; Naughton, Marybeth BS3

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Clinical Orthopaedics and Related Research: February 2012 - Volume 470 - Issue 2 - p 373-381
doi: 10.1007/s11999-011-2076-7
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THA over the past four decades has evolved to provide for pain relief and improved quality of life for a high percentage of patients. Although the incidence of infection and prosthetic loosening has decreased with improved surgical technique and implant design, polyethylene wear debris and osteolysis became a major limitation to prosthetic survivorship [12, 18, 24]. The extent of osteolysis has been linked to wear rate, which is affected by patient use [12, 36]. The foremost unresolved challenge has been the development of bearing surfaces that can withstand the higher demands of younger and more active patients and a population with greater longevity. New alterative bearings with greater wear resistance have been developed with the promise to reduce wear debris and extend implant longevity [8, 11]. These new low-wear bearings, which include highly cross-linked polyethylenes, metal on metal, and ceramic on ceramic, now have minimum 5-year results and have high survivorship [3, 4, 8, 9, 14, 31].

We previously published the 5- and 8-year results of this prospective randomized study comparing ceramic-on-ceramic bearing implants with metal-on-conventional polyethylene to determine whether the two bearings were at least equivalent in their performance [3, 8]. At 5 years, we reported equivalent Harris hip scores (96% versus 97%) but less osteolysis (1.5% versus 14%) and fewer revisions (2.7% versus 7.5%) in the ceramic cohorts. At 8 years, we reported higher survivorship for patients with ceramic bearings, a lower incidence of osteolysis, one ceramic fracture, and squeaking in three patients (1.5%).

At a minimum followup of 10 years, our primary objective was to confirm whether ceramic bearings are equal or superior to metal-on-polyethylene based on bearing survivorship. Our secondary objectives were the survivorship of implant systems, radiographic presence of osteolysis, and device squeaking.

Patients and Methods

In October 1996, a US Investigational Device Exemption, randomized, controlled noninferiority trial began comparing alumina-bearing couples with a chrome cobalt-on-polyethylene control system. The implant system design and study protocol have been reported [8]. Although all patients received the same femoral stem (Omnifit HA; Stryker Orthopaedics, Mahwah, NJ), there was a randomized one-third chance of receiving one of the three cup designs, two of which had an alumina-on-alumina bearing surface (System I or System II) and one the control (System III) (Fig. 1). The control polyethylene was gamma-sterilized in an inert atmosphere and was not highly cross-linked. Femoral head diameter for the ceramic cohorts was dictated by shell size and 89% were 32 mm or greater (Table 1). Head diameter for the polyethylene controls was left to the discretion of the surgeon and 90% were 28 mm in diameter.

Fig. 1:
The cementless components used in the ABC clinical study are shown. System I is a titanium porous-coated acetabular shell, with an alumina ceramic insert and an alumina ceramic femoral head. System II is a titanium arc-deposited, HA-coated acetabular shell, with an alumina ceramic acetabular insert and an alumina ceramic femoral head. The control system (denoted as System III) includes a titanium porous-coated acetabular shell, with a polyethylene acetabular insert and a cobalt-chrome femoral head.
Table 1:
Comparison of femoral head size for the three study groups

Five surgeons at five sites enrolled 253 patients (289 hips) and have followed 189 patients (216 hips) for a minimum of 10 years and average of 10.3 years. Before the 10-year anniversary, nine patients (11 hips) have died, 11 patients (11 hips) have been revised, and 44 patients (51 hips) withdrew and were lost to followup (LTF) between 5 and 10 years. Of those LTF, 20 patients (22 hips) opted out of continuing in the study at maximum 5 years and the latest evaluations for the remaining 24 patients (29 hips) occurred at 6 years for six hips; seven years for four hips; 8 years for three hips; and 9 years for 16 hips. There were 16 hips from System I, 20 hips from System II, and 15 hips from System III that were not included in the 10-year cohort. Statistical analysis showed no difference in distribution of demographics of LTF by study group compared with the minimum 10-year cohorts (diagnosis, gender, weight, height. body mass index) (Table 2).

Table 2:
Demographics for lost to followup

Kaplan-Meier (K-M) survivorship [25] was determined for bearing surface failure (fracture, revision for wear/osteolysis, locking mechanism failure), and end point revision for any reason.

The postoperative radiographs were assessed for standard parameters for cementless implants as recommended by the Hip Society [23] and reviewed by one orthopaedic surgeon (PB) who was not part of the study group. Hips were evaluated radiographically for radiolucent lines and osteolysis in acetabular component zones as described by DeLee and Charnley [10] and in all femoral Gruen zones [15] on AP and mediolateral radiographs. Implant stability was evaluated according to criteria described by Engh et al. [13]. Radiolucent line was defined as a lucent area in close proximity to the implant encompassing at least 50% of the zone and at least 1 mm in width. Implant migration was defined as prosthetic migration from fixed bony landmarks measured in 0.5-mm increments at each evaluation interval. Osteolysis was recorded for a specific area of bone loss (scalloping) without the presence of a reactive line for all implant zones.

Clinical data and radiographs were collected preoperatively, early postoperatively (at 6-8 weeks), and at every followup thereafter. A composite Harris hip score (HHS) was calculated [17] at each visit. History of squeaking, although not part of the original protocol, was recorded at last followup.

Baseline characteristics were summarized and compared among groups using Wilcoxon rank sum test for continuous data or Fisher’s exact test for discrete data. Mean HHS scores preoperatively and 10 years postoperatively were summarized and compared using one-way analysis of variance. Survival probability was estimated using the K-M method. The log rank test was used to test for differences of survival distribution function among three groups. When log rank test indicated there was a statistical difference (p < 0.05) in survival distribution function among groups, a Cox proportional hazards model was then used to compare survival among the three groups. Hazard ratios of System I and System II were displayed with System III as a reference. A hazard ratio (HR) of 1 would indicate no difference in risk, whereas a HR less than 1 indicates a lower risk. We performed a worse-case scenario K-M treating all patients lost to followup as failed. SAS software Version 9.2 (SAS Institute, Cary, NC) was used for all data analyses.


K-M survivorship for bearing-related revisions at 10 years postoperatively was similar (p = 0.152) for all three systems: System I was 100%, System II 98.6% (90.8%-99.8%), and System III 98.9% (92.3%-99.8%) (Fig. 2). The K-M survivorship at 10 years assuming all patients lost to followup showed no difference (p = 0.951) among three cohorts (Fig. 3). We revised one acetabular insert revision in ABC System II at 9.2 years as a result of a fractured ceramic insert. The patient was a 50-year-old woman at surgery with a body mass index of 23.2 kg/m2, an acetabular shell with 52-mm outer diameter, 32-mm insert (4-mm ceramic thickness), and acetabular cup inclination of 31°. There were three bearing-related revisions in ABC System III for osteolysis occurring at 4, 10.4, and 11 years after surgery.

Fig. 2:
The K-M survivorship with the end point bearing surface revision is no different for the three study groups at 10 years followup: System I, 100%; System II, 98.6% (90.8%-99.8%); and System III, 98.9% (92.3%-99.8%) (log rank test p = 0.152).
Fig. 3:
The K-M survivorship of the bearings, assuming lost to followup were revised, shows no statistical differences among the three groups (p = 0.951).

K-M survivorship revision for any reason at 10 years postoperatively was similar (p = 0.027) for all systems: System I was 97.9 (91.9%-99.5%), System II 95.2% (87.8%-98.2%), and System III 91.3% (83.4%-95.6%) (Fig. 4). In the analysis with System I and System II as independent categorical variables and System III as the reference group to test the HR (relative risk of revision), we found the HR (95% confidence interval) for System I was 0.183 (0.040-0.834) and for System II was 0.394 (0.124-1.257) compared with the control System III confirming the lower risk for revision for each ceramic cohort. The K-M survivorship (at 10 years) was repeated assuming that all patients lost to followup were revised to test the statistical difference under worst-case conditions and no statistical difference between study cohorts (log rank test p = 0.617) was found (Fig. 5).

Fig. 4:
The K-M survivorship with the end point revision for any reason is significantly different for the three study groups at 10 years followup: System I, 97.9% (91.9%-99.5%); System II, 95.2% (87.8%-98.3%); and System III, 91.3% (83.4%-95.6%) (log rank test p = 0.027).
Fig. 5:
The K-M survivorship end point revision for any reason, assuming all lost to followup were revised, shows no statistical differences among the three study groups (p = 0.617).

Six revisions for the 194 implanted hips in the ceramic-on-ceramic Systems I and II were performed (3.1%): two femurs with periprosthetic fracture and subsidence; one socket for recurrent dislocations at 5 years; two for deep joint infection; and one liner for fracture that occurred at 9 years postoperatively. Ten revisions (10.5%) for the control patients (95 hips) included one femur for periprosthetic fracture and one for leg length discrepancy; three acetabular revisions for recurrent dislocations; three for osteolysis; and two cases for deep joint infection (Table 3). In addition, three intraoperative ceramic chips that required intraoperative exchange of the acetabular component occurred at the time of surgery without any subsequent complications.

Table 3:
Component revisions for original population

All three groups had radiographically stable femoral implants and one acetabular component was unstable (Table 4). Femoral osteolysis in Gruen Zone 1, 7, 8, or 14 was noted in 26% of patients who received the control and in none of the patients who received ceramic Systems I or II (p < 0.001). Acetabular osteolysis occurred in 3.5% of controls and in 0% of the ceramic cohorts (p = 0.105). Radiolucencies were more commonly found about the microstructured titanium cups (p = 0.001) (Table 4).

Table 4:
Summary of radiographic results at 10 years

Mean HHSs in all three groups showed a marked improvement from preoperative status to last followup (Table 5). Squeaking has occurred in two patients (1%); a 66-year-old woman (System I) first noted noise at 6 years with hyperflexion and a 44-year-old man first noted the noise at 5 years. Neither patient can reproduce the squeaking, and the noise is of no clinical importance for these patients.

Table 5:
Demographics, clinical performance, less than 10-year followup, and complications


Ceramic bearings were introduced to reduce wear and increase long-term survivorship. Our current study is the only prospective randomized and controlled study with minimum 10-year followup comparing the survivorship of ceramic-on-ceramic with metal-on-polyethylene bearings. We previously reported equivalent HHSs but fewer revisions and less osteolysis comparing ceramic with the control polyethylene bearing [3, 8]. Our primary purpose was to confirm whether ceramic bearings were equal or superior to metal-on-polyethylene based on bearing survivorship and our secondary objectives were survivorship of implant systems, radiographic absence of osteolysis, and device squeaking.

Our study has some limitations. First, 44 patients (51 hips [16%]) withdrew before the 10-year anniversary. We have accounted for these patients in the survival analysis by considering them as failures. The possibility that all patients lost to followup were revised is unlikely because at last followup, all were doing well with intact implants. Statistical analysis showed no difference in distribution of patients lost by study group compared with the 10-year cohort indicating that the 10-year patient cohort was representative of the study population. Noninferiority to the control was maintained when looking at revision for bearing failure and at revision for any reason, previously identified as superior for the ceramic group, confirming at least equivalence of the bearing surfaces. Second, we had a single unblinded observer evaluating the radiographs and the evaluation for osteolysis and implant fixation are prone to intraobserver variability. We believe, however, that there is consistency in a single reviewer over a long-term study with an experienced orthopaedic surgeon. Third, 90% of the control subjects had a 28-mm head diameter compared with 11% of the ceramic cohorts. The use of smaller head sizes for the control patients may have influenced the higher dislocation and revision rate for the control patients and is consistent with a report in the literature [1]. However, the use of a 32-mm head size with conventional polyethylene might have resulted in more wear, osteolysis, and a higher revision rate [12, 18]. Finally, the five surgeons in this study were experienced with the implant systems used and the results may not be similar to a wider, less-experienced surgeon population.

We found the survival of implants with ceramic bearings to be similar to those of other reports in the literature of third-generation ceramic-on-ceramic bearings [5, 26-29, 32, 33) (Table 6). In our study, the survivorship of ceramic bearings (System I 100%, System II 99%) was no different than the control (99%) at 10 years and is similar to ceramic bearing survivorship reported in studies with 4- to 10-year followup. Murphy et al. [32] and Park et al. [33] reported 97% and 98% survivorship; and Lee et al. [27], Kress et al. [26] 99%, and Lewis et al. [28] 100% ceramic bearing survivorship. In our study, there have been no ceramic bearing failures beyond 10 years for either ceramic study group and no pending revisions. However, two additional hips from the control group were revised for osteolysis.

Table 6:
Comparison of ceramic bearing study results to recent reports on third-generation ceramic implant systems

Survivorship of implants in our study with regard to aseptic loosening aseptic is 99% for all three study cohorts (ceramic and controls). This high survivorship of the implants is similar to those of other studies using ceramic bearings with contemporary implant systems [5, 26-29, 32, 33]. Lusty et al. and Park et al. have reported 99% survivorship out to 9.6 years [29, 33] and Lee et al. have reported 100% survivorship at 10.9 years [27].

There is one unstable shell in the control group at 10 years in a patient who has evidence of acetabular osteolysis in Zones 1 and 2 and a radiolucent line of 3 mm in width in Zone 3. There are no unstable shells or pending failures in the ceramic group at 10 years.

Alumina-ceramic bearings have a history of problems with neck/socket impingement, a potential for fracture, and aseptic loosening [2, 16, 21, 30, 37]. Considering survivorship revision for any reason, our ceramic cohorts had a survivorship of 95% and 98% and is similar to those of recent publications and may reflect improvements in implant design and the material properties of the ceramic [7, 20]. Overall survivorship in recent reports ranges from 95% [33] to 99% [27]. However, the 91% survivorship of our control group was lower with instability (3%) and osteolysis (3%) representing the most common reasons for revision (Fig. 4). The use of smaller head sizes for the control patients may have played a role in the dislocation and revision rate and is consistent with a report in the literature [1]. Periprosthetic osteolysis with conventional polyethylene is reportedly the most common reason for revision surgery with a revision rate as high as 12% at 10 years [18, 19]. A recent report using a highly cross-linked polyethylene followed for 10 years showed no evidence of osteolysis [4]. In our study, at minimum 10 years, radiographic evidence for osteolysis is present in 26% of the control patients with only 3% being revised (Fig. 6A-B) and absent in the ceramic cohorts (Fig. 7). The low incidence of osteolysis in our patients with ceramic bearings is similar to recent reports [26-29, 32, 33]. Chevoillotte et al. found no osteolysis at 8.8 years, whereas Kress et al. reported 1% at 10.5 years [5, 26] (Table 6).

Fig. 6A-B:
(A) A 6-week postoperative radiograph of the hip of a 38-year-old woman with a control polyethylene bearing is shown. (B) A 4-year radiograph shows osteolysis in Zones 1, 7, and greater trochanter.
Fig. 7:
The patient was 48 years old at the time of implantation. His 12-year postoperative radiograph shows no osteolysis of the ceramic-ceramic bearing.

Cox regression analysis with System I and System II as independent categorical variables and System III as the reference group indicated a lower rate of revision for the ceramic groups as compared with the control group when all revisions were considered. In the worst-case analysis for revision for any reason based on assumption that all patients lost to followup were revised, the risk of revision for the ceramic groups is no longer lower than for the control metal/polyethylene group indicating at least comparable results for revision for any reason for the three study groups (Fig. 5).

The etiology of squeaking is believed to be multifactorial and related to patient age and size, surgical technique and implant position, stem design, and metallurgy [6, 22, 29, 34, 35, 38]. The incidence of squeaking in this ceramic study group is 1% and similar to recent reports [5, 26-28, 32, 33]. Chevoillotte et al. [5] reported a 6% incidence of squeaking, whereas Park et al. [33] at 9.6 years and Lewis et al. [28] at 8 years reported 0%. The low incidence in our study is believed to be related to the more rigid stem design and metallurgy used in our ceramic cohorts. This is supported by literature reports of a lower incidence of squeaking comparing stems with the same design and metallurgy with more flexible designs [22, 35, 38]. In both of the ceramic cohorts (Systems I and II), squeaking has not been a cause of disability, patient dissatisfaction, or need for revision.

Our observations support continued use of ceramic-on-ceramic bearings and provides a level of success at minimum 10 years followup for alternative bearings to compare. Continued clinical followup over the next decade will further measure the value of the hard-on-hard ceramic bearings for THA.


We thank the investigators who continue to follow our patients in the original ABC study: Benjamin E. Bierbaum, MD, New England Baptist Hospital (Boston, MA); James R. Roberson, MD, Emory Sports Medicine & Spine Center (Decauter, GA); and Robert Zann, MD, Boca Raton Hospital (Boca Raton, FL). We also thank the following individuals for their assistance: Peter Bonutti, MD, Bonutti Clinic, Effingham, IL; the independent radiographic reviewer for the study; and Jianhua Shen MS (Stryker, Mahwah, NJ), for performing the statistical analysis.


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