Skip to main content
PMC home page
Acta Orthopaedica logoLink to Acta Orthopaedica
. 2009 Jun 1;80(3):270–276. doi: 10.3109/17453670902967265

Stem subsidence of polished and rough double-taper stems

In vitro mechanical effects on the cement-bone interface

Ayumi Kaneuji 1,✉, Kengo Yamada 1, Kenichi Hirosaki 2, Masahiro Takano 2, Tadami Matsumoto 1
PMCID: PMC2823200  PMID: 19421909

Abstract

Background and purpose Many clinical reports have indicated that polished hip stems show better clinical results than rough stems of the same geometry. It is still unknown, however, what the mechanical effects are of different surface finishes on the cement at the cement-bone interface. We compared mechanical effects in an in vitro cemented hip arthroplasty model.

Methods Two sizes of double-taper polished stems and matt-processed polished stems (rough stems) were fixed into composite femurs. A 1-Hz dynamic load was applied to the stems for 1 million cycles. An 8-h no-load period was set after every 16 h of load. Stem subsidence within the cement, and compressive force and horizontal cement creep at the cement-bone interface, were measured.

Results Compared to rough stems, stem subsidence, compressive force and cement creep for polished stems were a maximum of 4, 12, and 7-fold greater, respectively. There was a strong positive correlation between stem subsidence and compressive force for polished stems. In contrast, a strong negative correlation was found between stem subsidence and compressive force for rough stems. There was also a statistically significant relationship between compressive force on the cement and cement creep for the polished stems, but no significant relationship was found for rough stems.

Interpretation This is the first evidence that different surface finishes of stems can have different mechanical effects on the cement at the cement-bone interface. Stem subsidence in polished stems resulted in compressive force on the cement and cement creep. The mechanical effects that polished taper stems impart on cement at the cement-bone interface probably contribute to their good long-term fixation and excellent clinical outcome.

Many studies have shown that the long-term survival of a polished stem is better than that of a rough-surfaced stem of the same geometry in cemented total hip arthroplasty (THA) (Dall et al.1993, Howie et al. 1998, Meding et al. 2000, Collis and Mohler 2002). The good long-term results of polished taper stems are probably attributable to the preservation of the proximal femoral cortex and such stems are associated with a low incidence of radiolucent lines in the proximal femur (Fowler et al. 1988, Wroblewski et al. 2001, Yates et al. 2002). Furthermore, using finite element analysis, it has been shown that polished prostheses give limited stem subsidence and cement creep (Verdonschot and Huiskes 1996, 1997, 1998, Lu and McKellop 1997, Norman et al. 2001), which may be beneficial. This suggests that stem subsidence without cement fracture observed in clinical practice, a phenomenon specific to polished taper stems (Fowler et al. 1988, Howie et al. 1998, Yates et al. 2002, Williams et al. 2002, Ek and Choong 2005), may be attributable to cement creep (Weightman et al. 1987). In a taper stem scenario, Lee (1990) hypothesized that the forces applied to the cement, to the cement-stem interface, and to the bone-cement interface may differ depending on the surface finish of the stem. The forces applied due to a rough stem are mainly tensile and shear forces, while for a polished stem they are mainly compressive. Assuming that this hypothesis is correct, these differences in the force applied to the cement and bone may explain the difference in clinical results for polished and rough stems. Lee's theory has, however, not been studied using a mechanical model. It is difficult to perform a comparative study in cadavers since bone quality, bone shape, and femoral canal size vary—which may influence the results. Furthermore, the characteristics of cement can change as a result of changes in temperature and humidity (Lee et al. 1990, Arnold and Venditti 2001). For this study, we used an in vitro simulated cemented hip replacement model to quantify the difference in stem subsidence of polished and rough surface-finished taper stems into the cement and to determine whether the surface finish has an influence on the mechanical effects of any differences in the cement.

Material and methods

Femoral stem implantation

We used composite femurs (no. 3303; Pacific Research Laboratories, Vashon, WA), which are similar in shape, mechanical characteristics, and material density to those of human femurs (Cristofolini et al. 1996, Heiner and Brown 2001). 4 stems were tested. 2 polished stems (size 2 and 3) and 2 rough stems (size 2 and 3) were implanted into one size of composite femur. The polished stem was the collarless polished taper stem (CPT stem; Zimmer, Warsaw, IN) tapered in the coronal and sagittal planes and with a surface roughness of 0.1 μm or less. The rough stem, with a surface roughness of 5.291 (SD 1.100) μm, was processed from the CPT stem by blowing glass beads using an air-blast machine (DP-5; Fuji Seiki Co.Ltd., Shizuoka, Japan) (Figure 1). A centralizer, dedicated to the CPT stem, was attached to the stem tip. The proximal transverse diameter and offset of the size-3 stem were larger than that of the size-2 stem (by 2.5 mm and 1 mm, respectively).

Figure 1.

Figure 1.

Open in a new tab

Collarless double-taper (CPT) stems. A polished stem is shown to the left and a matt-processed rough stem is shown to the right.

Mechanical testing

The composite femur neck was cut obliquely at 20 mm distal to the top of the greater trochanter and the distal part of the femur was cut at 230 mm from the top of the greater trochanter before attachment to the fixator. 8 pairs of 6-mm diameter holes were created in each of the medial, lateral, anterior, and posterior cortices of the femoral metaphysis and diaphysis. The uppermost hole was created at 10 mm distal to the femur neck cut. The distance between the upper and lower holes was 12 mm. A distance of 65 mm was provided between the proximal and distal parts. The upper holes were used for the placement of the rods containing the sensors to measure the compressive force, and the lower holes were used for placement of the rods containing the sensors to measure cement creep. After the holes were created, the composite femurs were immersed in blended vegetable oil for 24 h to simulate the humidity of an actual human femur.

Fixator

A fixator constructed of machine-structural-use carbon steel and epoxy resin was made, to secure the composite femur during testing. The epoxy resin was formed to the contours of the composite femur. Holes were positioned on the fixator so that they were aligned with those in the composite femur during testing. Thus, the rod protecting the measuring equipment could penetrate both the fixator and the composite femur, enabling measurement at a constant site. The rod that passed through the inner tube was fixed to the face of the medullary canal of the composite femur (Figure 2) and vacuum-mixed cement (Osteo-bond; Zimmer) was injected with a cement gun.

Figure 2.

Figure 2.

Open in a new tab

A composite femur fixed in the tester. Rods were set at the cement-bone interface.

A distal medullary plug was used before stem insertion. The stem was fixed with pressurized cement by 2 thumbs (the early cementing technique). After 24 h, the upper inner tube was replaced with the load cell, which was in direct contact with the cement-bone interface. The lower inner tube was removed. The temperature of the prepared femurs was maintained at 37oC using a heater and a temperature sensor attached to the epoxy resin.

Load

A dynamic sine wave load of 3,000 N was applied over 1 million cycles at a frequency of 1 Hz to the metal head fixed to the stem at 15 degrees to the coronal plane (Bergmann et al. 1993) using a hydraulically controlled fatigue tester (Instron Japan Co. Ltd., Kanagawa, Japan). The load of 3,000 N is equivalent to the load applied to the hip joint when a person weighing 70 kg stands on one leg. 1 million cycles of load application corresponds to 1 year of walking (Crowninshield et al. 1980, Zahiri et al. 1998). Assuming sleep time, a no-load period of 8 hours was provided every 16-h period of load application. The total load period for a stem was 19 days.

Mechanical assessment

Stem subsidence, and compressive force and cement creep at the cement-bone interface were measured (Figure 3). Stem subsidence was measured using a digital displacement gauge (DTH-A-5, 5 mm; Kyowa Electronic Instruments Co., Ltd., Tokyo, Japan) applied to the proximal lateral aspect of the stem. A positive value represented stem displacement in the distal direction. A load cell (TR20 I 500N/fs, TR20 I 200N/ fs; Kyowa) placed in the inner tube of the rod contacting the cement-bone interface was used to measure compressive force on the cement at this site. A positive value represented a horizontal force from the cement to the cortex.

Figure 3.

Figure 3.

Open in a new tab

A. An illustration of the tester. The measuring rod (R1 and R2) penetrating the fixator and the femur was placed at the cement-bone interface. Compressive force was measured with the load cell (Lc) via the upper rod (R1) in each site. The amount of cement creep was measured via the lower rod (R2). Stem subsidence was measured with the digital dial gauge (DG) contacting the upper end of the stem. B. The actual tester. The inside was inclined 15 degrees from the base on the coronary plane so that the load was applied to the femur head attached to the top of the stem from 15 degrees inside.

Cement creep was measured from the displacement of the measuring rod outward with a dial gauge (TM-1205; Teclock Co., Ltd., Nagano, Japan). The measuring range of the dial gauge was 1 to 5,000 μm and the error of the device was 0.5 μm. The technical error was ± 0.577 μm when 2 people took 3 measurements each. The value of cement creep was defined as the difference in the amount measured by the measuring rod installed at the cement-bone interface before and after the experiment.

Stem subsidence and compressive force were measured over time and the data was automatically entered into a computer using measurement collection and analysis software (sensor interface PCD-300A, Kyowa). 10,000 data sets corresponding to approximately 8 min were stored as one file per 30 min and a total of 912 files were collected. The data obtained were corrected and converted to distance and pressure units.

The periods of load and no load in a day were classified as 3 categories: early, middle, and late. Stem subsidence in each period was defined as the mean of the values collected in the 2 consecutive files (20,000 data sets) after the start of each period. The compressive force in each period was defined as the mean of the 960 (60 values/min × 8 min × 2 times) maximum values of sine waves collected in the 2 consecutive files after the start of each period. 57 (3 × 19 days) averaged values were used for analysis of stem subsidence and compressive force, respectively.

The stress relaxation value (Niels 1980, Lee at al. 1990) was defined as the difference between the mean of the minimum forces of sine waves in the 2 files collected in the late load period and the mean force in the 2 files collected in the late no-load period immediately afterwards. The final compressive force and stress relaxation values were obtained as the mean (SD) of the values on the final experiment day.

Statistics

The data were analyzed using SAS statistical analysis software (SAS Institute, Cary, NC). Inferential analysis was performed using the unpaired t-test and associations were examined using linear regression analysis and Pearson's correlation coefficient. A probability (alpha) of 5% was used to indicate statistical significance.

Results

The stem and cement pistoned vertically during load with an amplitude of 1 Hz. This pistoning was independent of the composite femur. This phenomenon was independent of surface finish and was observed in all stems.

Stem subsidence

The stem subsided only during the load period and it rose by a slightly smaller amount than the amount of subsidence during the no-load period (Table 1). All stems subsided progressively over time. The final stem subsidences for size-2 rough and polished stems were 0.274 mm and 1.179 mm, respectively. For size-3 rough and polished stems, the final subsidences were 0.334 mm and 0.521 mm, respectively. The subsidences were larger for the polished stem than for the rough stem: 4.3-fold with size 2 and 1.6-fold with size 3.

Table 1.

Stem subsidence

Load periods No-load periods
Polished size 2 0.218 (0.082) –0.148 (0.026)
Rough size 2 0.111 (0.023) –0.094 (0.014)
Polished size 3 0.160 (0.022) –0.141 (0.011)
Rough size 3 0.137 (0.018) –0.124 (0.008)
Open in a new tab

The values represent the mean stem subsidence (in mm (SD)) in 1 day of 19 days. A positive value in average movement means downward direction of the stem, and a negative value means upward direction of the stem.

Compressive force

The compressive force at the bone-cement interface, the force of the amplitude changed per 1 Hz during the load period. Such amplitude was not found during the no-load period. Differences in compressive forces among the measuring sites appeared as time elapsed, and relatively greater values were observed in the proximal medial and distal lateral portion. The compressive forces were relatively small in all other sites, including the anterior and posterior surfaces but excluding the proximal lateral site in the polished size-2 stem.

In the proximal medial site, for which the compressive force was observed most clearly, the force increased in the polished stem as time went on. However, the force remained low in the rough stem and it decreased in the size-2 rough stem (Figure 4). The compressive forces applied to the bone-cement interface on the final day were higher in the polished stem than in the rough stem, 12-fold in size 2 and 3.3-fold in size 3. Smaller compressive forces or reduction in compressive forces were also observed for the rough stem in the distal lateral sites. The compressive forces applied to the distal lateral sites were higher in the polished stem than the rough stem, by 2.9-fold in size 2 and 3.1-fold in size 3 (Table 2).

Figure 4.

Figure 4.

Open in a new tab

Compressive forces on the bone-cement interface. PM: proximal medial site; PL: proximal lateral site; DM: distal medial site; DL: distal lateral site.

Table 2.

Final compressive force and cement creep at the cement-bone interface

Proximal–medial Distal–medial Proximal–lateral Distal–lateralt Proximal–anterior Distal–anterior Proximal–posterior Distal–posterior
Polished size 2 force 435 (1.7) 1.7 (0.1) 78 (6.5) 117 (0.3) 4.4 (0.3) 2.2 (0.1) 2.7 (0.2) 11 (0.7)
creep 215 1.0 27 152 –4.0 –14 –0.3 35
Rough size 2 force 36 (2.2) –1.0 (0.1) 17 (1.1) 58 (2.3) 3.5 (0.5) 1.3 (1.1) 2.0 (0.3) 4.4 (1.1)
creep 29 –33 11 46 26 10 8.0 22
Polished size 3 force 179 (3.7) –1.3 (0.3) 29 (0.4) 75 (1.1) 5.2 (0.2) 1.9 (0.3) 9.0 (1.4) –6.6 (0.5)
creep 90 –4.0 16 23 –1.0 –0.3 11 –19
Rough size 3 force 55 (3.0) 1.0 (0.1) 16 (0.1) 24 (1.2) 8.4 (0.6) 0.8 (0.1) 3.4 (0.4) 4.7 (1.6)
creep 34 –19 20 10 –0.3 –1.0 –0.3 3.6
Open in a new tab

The final compressive force is the mean value (SD) of the 960 times of maximum values of 1 Hz sine wave of the late period in the final experiment day, and the cement creep was the mean value (SD) of three times measurements in each site. The values are the average N (SD) of the force and the average micron meter (SD) of the cement creep.

A statistically significant regression was observed between the stem subsidence and compressive force at the proximal medial site with all stems. A significant positive correlation was found between stem subsidence and compressive force in the polished stems while a significant negative correlation was found in the rough stems. This suggests that subsidence of the polished stem may lead to an increase in compressive force at the bone-cement interface while subsidence of the rough stem may induce a decrease in compressive force (Figure 5).

Figure 5.

Figure 5.

Open in a new tab

Stem subsidence and compressive force at the cement-bone interface. Stem subsidence in each period was defined as the mean of values in the two consecutive files (20,000 data sets) after the start of each period. The compressive force in each period was defined as the mean of the collected 960 maximum values of sine waves in the two consecutive files after the start of each period. 57 (3 periods x 19 days) averaged values were used for analysis of stem subsidence and the compressive force, respectively. Simple regression analysis, significances, and correlation coefficients (r): P2; y = 369.44x – 3.5987, R2 = 0.935, p < 0.001, r = 0.9667. P3; y = 191.92x + 66.66, R2 = 0.536, p < 0.001, r = 0.7322. R2; y = –347.08x + 128.55, R2 = 0.779, p < 0.001, r = 0.8837. R3; y = –244.51x + 138.91, R2 = 0.8633, p < 0.001, r = 0.9291. y: force; x: stem subsidence, R2 = r2.

Cement creep

The amount of cement creep was appreciable at the sites where large compressive forces were observed: proximal medial and distal lateral sites. The cement creep was larger in the polished stem than in the rough stem, by 7.4-fold and 2.6-fold in size 2 and 3 stems at the proximal medial site and by 3.3-fold and 2.3-fold in size 2 and 3 stems at the distal lateral site (Table 2). The greatest degree of cement creep (of 215 μm) was observed at the proximal medial site of the size 2 polished stem.

In the simple regression analysis, a statistically significant relationship between the compressive force (x) and cement creep (y) of 4 proximal and 4 distal sites was found in the polished stems (size 2: y = 0.672x + 8.085, R2 = 0.822, p < 0.002; size 3: y = 0.520x – 0.852, R2 = 0.887, p < 0.001) while it was not significant in the rough stems (size 2: y = 0.487x + 4.832, R2 = 0.449, p = 0.07; size 3: y = 0.337x – 0.967, R2 = 0.407, p = 0.09). This suggests that the compressive force caused cement creep in the polished stems.

Stress relaxation

Stress relaxation occurring between the late load period and the late no-load period, namely, the amount of relaxation of the stress accumulated in the cement, was evaluated in the proximal medial site where the compressive force was largest. The amount of stress relaxation tended to increase over time in the polished stems whereas it did not increase in the rough stems (Figure 6). The stress relaxation value on the final day was 104 (SD 2.2) N and 37 (SD 2.2) N in the polished stems (sizes 2 and 3, respectively) whereas it was 6.4 (SD 1.2) N and 17 (SD 1.1) N in the rough stems. Thus, the final stress relaxation was larger in the polished stems than in the rough stems by 16-fold in size 2 and 2.2 -fold in size 3.

Figure 6.

Figure 6.

Open in a new tab

Stress relaxation at proximal medial site. Color codes, see Figure 5. The stress relaxation value in a day was defined as the difference between the mean of the 960 minimum forces of sine waves in the 2 files collected in the late load period and the mean of the 960 minimum forces in the 2 files collected in the late no-load period. A total 19 values were collected for data in each stem.

Discussion

We found that the surface finish of the cemented stem creates a difference in the dynamic behavior. In the polished stems, there were correlations between stem subsidence and degree of compressive force and cement creep. We suggest that subsidence of the stem gradually presses the cement toward the periphery of the medullary canal, which leads to cement creep. Thus, compressive force tends to be applied to the cement-bone interface, which support a theory suggested in the past (Fowler et al. 1988, Lee 1990, Yates et al. 2002). In contrast to the polished stem, we found a negative correlation between stem subsidence and compressive force in the rough stem. This suggests that the shear force on the bone-cement interface pulls the cement toward the inside of the medullary canal, and we speculate that stem subsidence of the rough stem tends to cause the reduction in compressive force on the cement-bone interface.

We have found no earlier reports in which cement creep was measured in a THA model. In our study, we used vacuum-mixed cement that is used in clinical practice, which may enhance cement durability (Alkire et al. 1987, Wixson et al. 1987). Although Norman et al. (1995) reported that vacuum mixing reduces creep strain by 48%, we found a maximum of 215 μm of cement creep using vacuum-mixed cement, which suggests that similar cement creep occurs in vivo. Kaneuji et al. (2006) reported that improvement of radiolucency in the CPT stem is prominent in Gruen zone 7. We also found larger compressive force and creep in zone 7.

Stress relaxation is defined as a change in stress level over time at constant strain (Niels 1980, Lee 1990). In other words, stress relaxation is considered to be the decrease in strain energy accumulated in cement that has crept by stem subsidence. Greater relaxation of strain energy can result in greater ability in self-protection against fatigue breakage (Niels 1980, Lee 1990). Clinically, the opportunity for strain energy relaxation such as during sleep is important, as the stress relaxation tends to occur during the no-load period (Lu and McKellop 1997). The stress relaxation was reproduced in our THA model, and the pattern in the polished stems was different from that in the rough stems. We found that stress relaxation remains high over time in the polished stem. This may be one of the reasons for there being less failure with the polished stem in clinical practice.

Clinical radiostereometric analyses and reports on retrieved femoral implants (Alfaro-Adrian et al. 1999, Howell et al. 2004), and also the report on the mechanical experiment that evaluated stem subsidence and micromotion in THA models (Ebramzadeh et al. 2004), suggest that subsidence and micro-motion can also be found in the unloosened rough stem, though the amount is smaller compared to the polished stem. The polished stem is less likely to damage the cement interface when it moves in synchrony with amplitude (Howell et al. 2004). The mirror-like surface of the polished stem enables the cement to fit perfectly, allowing no micro-gap and no space for debris passage (Crawford et al. 1999). On the other hand, repeated micromotions in the matt finished rough stem could cause micro-fracture of cement and cement debris, and produce a passage for wear particles down to the femoral canal (Crawford et al. 1999, Howell et al. 2004). We were able to show the occurrence of micromotion. Although the final amount of stem subsidence was larger in the polished stem than in the rough stem, daily subsidence and rise in the rough stem were more than 0.1 mm and almost the same as those for the polished stem. One possible cause of difference in the amount of final stem subsidence was that the stem tended to return to the original position during the period with no load. Each stem has a hollow centralizer at the bottom, to allow for stem slip without cement breakage. Polished stems slipped in the cement and centralizer during loading, and the stems tend to maintain their position through cement creep and stress relaxation. However, rough-surface stems do not slip easily in the cement and centralizer because of micro-bonding of the rough surface with the cement, and the stems tend to return to their original position during the periods of no load. As a result of this difference, we consider the centralizer to be effective for polished stems, but less effective for rough stems.

The forces at the proximal medial and distal lateral sites were stronger than at other sites, probably because the load was applied to the stem in our model only in one direction in the coronal plane. In other words, the load was transmitted to the calcar region and the moment was reflected as the counter reactive force on the distal lateral site.

The small stem had a thicker cement mantle than the large one, because same size of composite femur was used for all stems. More subsidence and compressive force were seen in the small-size polished stem than in the large one. This may indicate that a small stem is likely to subside into cement more than a large one. However, we cannot conclude this because we only studied a small number of stems. We believe that the differences in results according to stem size in each surface-finish group had some range of variation. However, our study indicates differences between polished and rough surface stems because the results in each surface finish group showed a similar pattern (but a different pattern in the other one). The correlation between stem subsidence and compressive force is the most important and obvious difference. Each final value of stem subsidence and compressive force is the mean value of a large amount of data with a small range of standard deviation. Thus, we believe that the same pattern in the same surface finish group and the opposite pattern in the other surface finish group indicated a real difference, even with the small number of stems.

The most important finding of our study was that cement creep, stress relaxation, and reverse subsidence occur during the periods of no load. These have not been measured in previous studies. However, it was impossible to measure the shear force, i.e. vertical force, with the load cell. If the shear force is measured, the mechanism of loosening can be explained more easily.

Future studies should include a long-term comparison of more stems, loading in different directions, and trying to measure shear stress at the interface. However, the theoretically predicted behavior of the cemented collarless double-taper stem was verified in our study and the results may lead to a better understanding of loosening mechanisms in cemented stems.

Acknowledgements

AK: study design, analysis of data, and manuscript preparation. KY: gathering and analysis of data, and manuscript preparation. KH and MT: technical advice and operation of testing machine. TM: study design, and ensuring the accuracy of the data and analysis.

We are grateful to Mr Hiroshi Ishiyama (Specialty Products and Technical Services, Zimmer K.K.) for production of the tester and for his technical support during this study.

All tests were performed by the authors. Zimmer K.K. provided the tester and materials at no charge. The company did not participate in the design of the study, in evaluation of the results, or in writing of the manuscript. No funding or remuneration was received by the authors for this study.

References

  1. Alfaro-adrian J, Gill HS, Murray DW. Cement migration after THR. A comparison of Charnley Elite and Exeter femoral stems using RSA. J Bone Joint Surg (Br) 1999;81:130–4. doi: 10.1302/0301-620x.81b1.8904. [DOI] [PubMed] [Google Scholar]
  2. Alkire MJ, Dabezies EJ, Hastings PR. High vacuum as a method of reducing porosity of polymethylmethacrylate. Orthopedics. 1987;10:1533–9. [PubMed] [Google Scholar]
  3. Arnold JC, Venditti NP. Effects of environment on the creep properties of a poly(ethylmethacrylate) based bone cement. J Mater Sci Mater Med. 2001;12:707–17. doi: 10.1023/a:1011272626846. [DOI] [PubMed] [Google Scholar]
  4. Bergmann G, Graichen F, Rohlmann A. Review article. Hip joint loading during walking and running, measured in two patients. J Biomech. 1993;26:969–90. doi: 10.1016/0021-9290(93)90058-m. [DOI] [PubMed] [Google Scholar]
  5. Collis DK, Mohler CG. Comparison of clinical outcomes in total hip arthroplasty using rough and polished cemented stems with essentially the same geometry. J Bone Joint Surg (Am) 2002;84:586–92. doi: 10.2106/00004623-200204000-00012. [DOI] [PubMed] [Google Scholar]
  6. Crawford RW, Evans M, Ling RS, Murray DW. Fluid flow around model femoral components of differing surface finishes: in vitro investigations. Acta Orthop Scand. 1999;70:589–95. doi: 10.3109/17453679908997847. [DOI] [PubMed] [Google Scholar]
  7. Cristofolini L, Viceconti M, Cappello A, Toni A. Mechanical validation of whole bone composite femur models. J Biomech. 1996;29:525–35. doi: 10.1016/0021-9290(95)00084-4. [DOI] [PubMed] [Google Scholar]
  8. Crowninshield RD, Brand RA, Johnston RC, Milroy JC. The effect of femoral stem cross-sectional geometry on cement stresses in total hip reconstruction. Clin Orthop. 1980;(146):71–7. [PubMed] [Google Scholar]
  9. Dall DM, Learmonth ID, Solomon MI, Miles AW, Davenport JM. Fracture and loosening of Charnley femoral stems. Comparison between first-generation and subsequent designs. J Bone Joint Surg (Br) 1993;75:259–65. doi: 10.1302/0301-620X.75B2.8444947. [DOI] [PubMed] [Google Scholar]
  10. Ebramzadeh E, Sangiorgio SN, Longjohn DB, Buhari CF, Dorr LD. Initial stability of cemented femoral stems as a function of surface finish, collar, and stem size. J Bone Joint Surg (Am) 2004;86:106–15. doi: 10.2106/00004623-200401000-00016. [DOI] [PubMed] [Google Scholar]
  11. Ek ET, Choong PF. Comparison between triple-tapered and double-tapered cemented femoral stems in total hip arthroplasty: a prospective study comparing the C-Stem versus the Exeter Universal early results after 5 years of clinical experience. J Arthroplasty. 2005;20:94–100. doi: 10.1016/j.arth.2004.08.012. [DOI] [PubMed] [Google Scholar]
  12. Fowler JL, Gie GA, Lee AJ, Ling RS. Experience with the Exeter total hip replacement since 1970. Orthop Clin North Am. 1988;19:477–89. [PubMed] [Google Scholar]
  13. Heiner AD, Brown TD. Structural properties of a new design of composite replicate femurs and tibias. J Biomech. 2001;34:773–81. doi: 10.1016/s0021-9290(01)00015-x. [DOI] [PubMed] [Google Scholar]
  14. Howell JR, Jr, Blunt LA, Doyle C, Hooper RM, Lee AJ, Ling RS. In vivo surface wear mechanisms of femoral components of cemented total hip arthroplasties: the influence of wear mechanism on clinical outcome. J Arthroplasty. 2004;19:88–101. doi: 10.1016/s0883-5403(03)00278-x. [DOI] [PubMed] [Google Scholar]
  15. Howie DW, Middleton RG, Costi K. Loosening of matt and polished cemented femoral stems. J Bone Joint Surg (Br) 1998;80:573–6. doi: 10.1302/0301-620x.80b4.8629. [DOI] [PubMed] [Google Scholar]
  16. Kaneuji A, Sugimori T, Ichiseki T, Fukui K, Yamada K, Matsumoto T. The relationship between stem subsidence and improvement in the radiolucency in polished tapered stems. Int Orthop. 2006;30:387–90. doi: 10.1007/s00264-006-0112-0. [DOI] [PMC free article] [PubMed] [Google Scholar]
  17. Lee AJC. The time-dependent properties of polymethylmethacrylate bone cement: the interaction of shape of femoral stems surface finish and bone cement. In: Learmonth ID, editor. Interfaces in Total Hip Arthroplasty. Springer-Verlag Co.; London etc: 1990. pp. 11–9. [Google Scholar]
  18. Lee AJC, Perkins RD, Ling RSM. Time-dependent properties of polymethylmethacrylate bone cement. In: Older J, editor. Implant Bone Interface. Springer-Verlag Co.; Berlin etc: 1990. pp. 85–90. [Google Scholar]
  19. Lu Z, Mckellop H. Effects of cement creep on stem subsidence and stresses in the cement mantle of a total hip replacement. J Biomed Mater Res. 1997;34:221–6. doi: 10.1002/(sici)1097-4636(199702)34:2<221::aid-jbm11>3.0.co;2-l. [DOI] [PubMed] [Google Scholar]
  20. Meding JB, Nassif JM, Ritter MA. Long-term survival of the T-28 versus the TR-28 cemented total hip arthroplasties. J Arthroplasty. 2000;15:928–33. doi: 10.1054/arth.2000.9319. [DOI] [PubMed] [Google Scholar]
  21. Niels JH. The relaxation of some acrylic bone cement. Acta Orthop Scand. 1980;51:727–31. doi: 10.3109/17453678008990867. [DOI] [PubMed] [Google Scholar]
  22. Norman TL, Kish V, Blaha JD, Gruen TA, Hustosky K. Creep characteristics of hand-and vacuum-mixed acrylic bone cement at elevated stress levels. J Biomed Mater Res. 1995;29:495–501. doi: 10.1002/jbm.820290409. [DOI] [PubMed] [Google Scholar]
  23. Norman TL, Thyagarajan G, Saligrama VC, Gruen TA, Blaha JD. Stem surface roughness alters creep induced subsidence and ‘taper-lock’ in a cemented femoral hip prosthesis. J Biomech. 2001;34:1325–33. doi: 10.1016/s0021-9290(01)00085-9. [DOI] [PubMed] [Google Scholar]
  24. Verdonschot N, Huiskes R. Subsidence of the stems due to acrylic cement creep is extremely sensitive to interface friction. J Biomech. 1996;29:1569–75. [PubMed] [Google Scholar]
  25. Verdonschot N, Huiskes R. Acrylic cement creeps but does not allow much subsidence of femoral stems. J Bone Joint Surg (Br) 1997;79:665–9. doi: 10.1302/0301-620x.79b4.7173. [DOI] [PubMed] [Google Scholar]
  26. Verdonschot N, Huiskes R. Surface roughness of debonded straight-tapered stems in cemented THA reduces subsidence but not cement damage. Biomaterials. 1998;19:1773–9. doi: 10.1016/s0142-9612(98)00088-x. [DOI] [PubMed] [Google Scholar]
  27. Weightman B, Freeman MA, Revell PA, Braden M, Albrektsson BE, Carlson LV. The mechanical properties of cement and loosening of the femoral component of hip replacements. J Bone Joint Surg (Br) 1987;69:558–64. doi: 10.1302/0301-620X.69B4.3611159. [DOI] [PubMed] [Google Scholar]
  28. Williams HD, Browne G, Gie GA, Ling RS, Timperley AJ, Wendover NA. The Exeter universal cemented femoral component at 8 to 12 years. J Bone Joint Surg (Br) 2002;84:324–34. doi: 10.1302/0301-620x.84b3.12261. [DOI] [PubMed] [Google Scholar]
  29. Wixson RL, Lautenschlager EP, Novak MA. Vacuum mixing of acrylic bone cement. J Arthroplasty. 1987;2:141–9. doi: 10.1016/s0883-5403(87)80021-9. [DOI] [PubMed] [Google Scholar]
  30. Wroblewski BM, Siney PD, Fleming PA. Triple taper polished cemented stem in total hip arthroplasty: rationale for the design, surgical technique, and 7 years of clinical experience. J Arthroplasty (Suppl 1) 2001;16:37–41. doi: 10.1054/arth.2001.28374. [DOI] [PubMed] [Google Scholar]
  31. Yates P, Gobel D, Bannister G. Collarless polished tapered stem: clinical and radiological follow-up over 5 years. J Arthroplasty. 2002;17:189–95. doi: 10.1054/arth.2002.30292. [DOI] [PubMed] [Google Scholar]
  32. Zahiri CA, Schmalzried TP, Szuszczewicz ES, Amstutz HC. Assessing activity in joint replacement patients. J Arthroplasty. 1998;13:890–5. doi: 10.1016/s0883-5403(98)90195-4. [DOI] [PubMed] [Google Scholar]

Articles from Acta Orthopaedica are provided here courtesy of Nordic Orthopaedic Federation

RESOURCES