Study of bone remodeling of two models of femoral cementless stems by means of DEXA and finite elements
© Gracia et al; licensee BioMed Central Ltd. 2010
Received: 9 December 2009
Accepted: 28 May 2010
Published: 28 May 2010
A hip replacement with a cemented or cementless femoral stem produces an effect on the bone called adaptive remodelling, attributable to mechanical and biological factors. All of the cementless prostheses designs try to achieve an optimal load transfer in order to avoid stress-shielding, which produces an osteopenia.
Long-term densitometric studies taken after implanting ABG-I and ABG-II stems confirm that the changes made to the design and alloy of the ABG-II stem help produce less proximal atrophy of the femur. The simulation with FE allowed us to study the biomechanical behaviour of two stems. The aim of this study was, if possible, to correlate the biological and mechanical findings.
Both models with prostheses ABG-I and II have been simulated in five different moments of time which coincide with the DEXA measurements: postoperative, 6 months, 1, 3 and 5 years, in addition to the healthy femur as the initial reference. For the complete comparative analysis of both stems, all of the possible combinations of bone mass (group I and group II of pacients in two controlled studies for ABG-I and II stems, respectively), prosthetic geometry (ABG-I and ABG-II) and stem material (Wrought Titanium or TMZF) were simulated.
Results and Discussion
In both groups of bone mass an increase of stress in the area of the cancellous bone is produced, which coincides with the end of the HA coating, as a consequence of the bottleneck effect which is produced in the transmission of loads, and corresponds to Gruen zones 2 and 6, where no osteopenia can be seen in contrast to zones 1 and 7.
In this study it is shown that the ABG-II stem is more effective than the ABG-I given that it generates higher tensional values on the bone, due to which proximal bone atrophy diminishes. This biomechanical behaviour with an improved transmission of loads confirmed by means of FE simulation corresponds to the biological findings obtained with Dual-Energy X-Ray Absorptiometry (DEXA).
The implantation of a cemented or cementless femoral stem implies an important change in the physiological load distribution. The bone reacts to the new situation, in accordance with Wolff's law, undergoing a process of adaptive remodelling , related to both mechanical and biological factors, being the most important the initial bone mass .
Long term studies of different cementless stems show a high incidence of stress-shielding, caused by the change in the distribution of loads on the femur [3–5]. The monitoring of an anatomic femoral stem with metaphyseal load-bearing and HA coating (ABG-I), that was carried out through a prospective, controlled study that included 67 patients (Group I) in the period 1994-99, has confirmed that even though the clinical results are very favourable, a high percentage of cases with stress-shielding are detected . This results in a proximal atrophy which has been quantified with DEXA . For that reason the stem has been redesigned (ABG-II) in an attempt to improve the proximal transfer of loads and reduce the phenomenon of stress-shielding. The main differences between both stems concern geometrical design and material. The overall lenght has been reduced by 8% and the proximal and distal diameters by 10%. The prosthesis shoulder has been modified. The material has changed from Wrought Titanium (Ti 6Al-4V) alloy to TMZF (Titanium, Molybdenum, Zirconium and Ferrous) alloy.
A similar design study was done with the ABG-II stem in the period 2000-05, with 69 patients of comparable demographic characteristics than the previous one (Group II). In both studies the surgical technique, post-operative rehabilitation program, densitometry studies and statistical analysis were identical . The study confirmed less proximal atrophy, therefore one could ask if the new design has effectively improved the load transfer conditions in the proximal femur, producing less stress-shielding. The simulation with Finite Elements (FE) allows us to verify the correlation between the mechanical stimulus and the changes detected in the bone density. In order to do this, the evolution of the mechanical stimulus over a period of 5 years has been analysed, correlating the findings with the quantified Bone Mineral Density (BMD) evolution in the studies using DEXA.
Once the three meshes had been generated in I-deas (healthy femur, prosthesis ABG-I and operated femur), the prosthesis was positioned in the femur always taking the mesh of the operated femur as the base. From the previous process of modelling on the cadaveric femur, only the cortical bone was used, from which the cancellous bone was modelled again, in such a way that it fit perfectly to the contact with the prosthesis (Figure 2, ABG-I model). Work with the ABG-II prosthesis was undertaken in the same way (Figure 2, ABG-II model).
The program Abaqus 6.7  was used for the calculation, with the Abaqus Viewer being used for the results postprocessing. It was necessary to undertake a contact simulation between the prosthesis and the cancellous bone for which a friction coefficient of 0.5 was considered simulating the press-fit setting according with . In light of the former results a sensitivity analysis was carried out in order to determine the appropriate interface conditions, considering several friction coefficient values from 0.2 to 0.5 in steps of 0.05, obtaining significative differences in the analyzed range, but with similar results from 0.4 to 0.5. It was observed that the value of 0.5 corresponds practically to a bonded interface, but with the advantage that allows moving apart the stem from the bone in higher tension zones, providing a more realistic stress distribution inside the bone.
The final model with ABG-I stem comprises a total of 60401 elements (33504 for cortical bone, 22088 for cancellous bone and 4809 for ABG-I stem). The final model with the ABG-II stem is made up of 63784 elements (33504 for cortical bone, 22730 for cancellous bone and 7550 for ABG-II stem).
Three boundary conditions were defined: clamped in the medial diaphyseal part of the femur, force on the prosthetic head due to the reaction of the hip caused by the weight of the person (400% BW) and force on the greater trochanter (200% BW) generated by the abductor muscles .
Mechanical properties of materials
MAXIMUM COMPRESSION STRESS
20000 15, 20, 21
0.3 16, 18
150 16, 18
90 16, 18
23 16, 18
1 16, 18
0.3 16, 18
74000 - 85000 22
For the complete comparative analysis of both stems, all of the possible combinations of bone mass (group I, ABG-I, 67 patients in the period 1994-99 and group II, ABG-II, 69 patients in the period 2000-05) prosthetic geometry (ABG-I and ABG-II) and stem material (Wrought Titanium or TMZF) were simulated. This way it was possible to compare the mechanical performance of both prostheses in what refers to the transmission of loads and the interaction in the bone-prosthesis contact zone. It also makes it possible to distinguish the most influential parameter (geometry or material) for the design of future prosthetic stems.
The average von Mises stress is used, given that despite not distinguishing between tension and compression values, it is sufficiently indicative of the tendency of the mechanical stimulus and it is standard in FE software.
Both models with prostheses ABG-I and II have been simulated in five different moments of time which coincide with the DEXA measurements: postoperative, 6 months, 1, 3 and 5 years, in addition to the healthy femur as the initial reference. In both groups of bone mass an increase of stress in the area of the cancellous bone is produced, which coincides with the end of the HA coating, as a consequence of the bottleneck effect which is produced in the transmission of loads, and corresponds to Gruen zones 2 and 6, where no osteopenia can be seen in contrast to zones 1 and 7.
BMD evolution in the operated and healthy hip is shown in Figure 3 for both prostheses. For ABG-I, the preoperative measurements performed in both hips showed slightly higher BMD rates in the healthy hip, although these were not statistically significant. Postoperative values were taken as a reference for the operated hip. Differences between 2.66 and 10.01% in respect to those measurements taken before surgery were found and attributed to bone loss due to the surgical procedure. A decrease in BMD was detected in all zones except zone 4, six months after surgery. Between 6 and 12 postoperative months there was a slight additional loss of BMD in zones 1 and 7, but some bone recovery in the middle and distal areas around the implant. No significant changes in BMD were observed in zones 1 to 6 from the end of the first year to the end of the fifth year.
For ABG-II, the preoperative measurements performed in both hips showed again slightly higher bone density rates in the healthy hip, ranging between 2.2% in zone 5 to 4.1% in zone 2, although these were not statistically significant. Differences between 0.63 and 6.43% in respect to those measurements taken before surgery were found and attributed as in the ABG-I case to bone loss due to the surgical reaming and rasping. No changes or a minimal decrease in bone density was detected in zones 1 to 6, six months after surgery, attributed to rest period, partial weight bearing and the later effects of surgery. The bone loss was statistically significant only in zone 7. A slight additional loss of bone density was observed in zone 7, as well as some bone recovery in the middle and distal areas around the implant. Minor changes in bone density were observed in zones 1 to 6 from the end of the first year to the end of the fifth year. The bone mass remains stable in this period, with a little bone recovery in zones 2 and 6. Nevertheless, there was some decrease in zone 7 in the period between the first and fifth year, when a loss of 23.88% can be reached. The bone density in the contra-lateral healthy hip (bone mass group II) showed some slight differences during the follow-up, with decreases between 1.4 and 2.7%, more evident in the proximal part of the femur, richer in cancellous bone. The values obtained for zones 3 to 5 were similar to those of the operated femurs; in zones 2 and 6 they were slightly superior; only zones 1 and 7 showed significant differences.
A tensional increase is noticeable in the whole area close to the lesser trochanter with the use of the ABG-II stem, as well as the tensional increase that the insertion of the ABG-II prosthesis involves with respect to the ABG-I. These differences can be observed in a more clear way in Figures 4 and 5. In both figures it is clearly noticeable that the result corresponding to the two material for every stem are practically the same (superimposed lines); however, the results corresponding to both geometrical designs (ABG I, ABG II) are different, with a higher tensional level for the ABG II stem.
It could be checked that in every case the stress corresponding to the ABG-II stem is greater than the one resulting from the insertion of the ABG-I stem (Figures 4 and 5). In the figures it can be seen that in every zone and for any time the stress achieve higher values in ABG-II than in ABG-I stem. This way it is possible to confirm that with the second generation of stem (ABG-II) the stress increases in practically every zone with this increase being most evident in zone 7.
When a hip arthroplasty is carried out the initial tensional state of the joint is modified. In the healthy femur, the loads are transferred from the femoral head to the lesser trochanter, which distributes the compressive forces to the femoral diaphysis . This way the primary trabecular bundles on the healthy femur are identified: the arch shape, formed by tension forces and the principal compression group of Delbet, formed by compression forces . This model of loads is inverted after the implant. It is confirmed that the stresses are transferred fundamentally from the prosthetic head to its stem, producing stress-shielding and loading the femur mainly in the areas which correspond with the end of the HA coating (Figure 4 and 5).
The simulation using FE makes it possible to explain the biomechanical changes produced in the femur after the implant of a prosthetic stem and establish an evident parallelism between the results obtained in the study with DEXA and the results from the study with FE, as can be seen in Figure 6. The bone mass variation and the tensional evolution in each one of the Gruen zones obtained by simulation follow similar paths.
An essential point in the models concerns the loads. The most significant correspond to the gluteus medium muscle, iliotibial tract and psoas major muscle or solely the action of the abductor muscles. For this study the final option was chosen in accordance with the majority of authors [23, 27]. Different authors have studied the biomechanics of the hip from the point of view of contact and muscle forces [28–30]. So, according to Bergmann , the peak force is 330% of body weight (BW) when going downstairs, nevertheless he accepts that higher peaks could be observed (409% of BW during walking) when muscle dysfunction exists .
If the principal stress flows (tension/compression) are represented in the models with stem, it is possible to verify how the zone subjected to tension is found on the lateral surface of the femur, and the zone subjected to compression is on the internal face of the femur due to the eccentricity of the load. It is also possible to appreciate how the load is transferred from the prosthetic head to the femur, favouring a greater concentration of loads on the implanted bone with the ABG-II stem as opposed to the one implanted with the ABG-I stem. HA coating has no influence in BMD maintenace and evolution. Its only purpose is facilitating the osseointegration and providing a better press-fit in the metaphyseal zone .
In the analysis carried out with respect to material, it has been shown that the use of a new Titanium TMZF alloy does not produce any significant changes in respect to the alloy used in the ABG-I prosthesis. The reason for this is due to the fact that in both cases, the modulus of elasticity is three orders of magnitude greater than that of the modulus of elasticity of the cancellous bone, which is the bone in contact with the stem, for which the mentioned variation in the elastic modulus of the prosthesis is insufficient to provide noticeable changes. In short, the results are much more sensitive to the geometric design than to the material properties.
The results show that the ABG-II prosthetic stem is more effective than the ABG-I given that it generates higher tensional values on the bone (Figures 4 and 5), due to which the proximal bone atrophy diminishes. This biomechanical improvement with a better transmission of loads corresponds with the biological findings obtained with DEXA. We agree with  that a greater conservation of the proximal bone is an important biological factor, which brings about less bone atrophy in the long term. In accordance with , we agree that the discreet reduction in the length of the stem does not have any influence on the transmission of loads; however, it requires a more refined surgical technique to avoid the varus positioning.
Studies with DEXA in a longer term (10 years) should be needed to determine the influence of stress-shielding on adaptive bone remodelling in long term. Since this work reproduces the mechanical behaviour of two femoral stems placed in a neutral position in the femur, further studies should be addressed to determine the mechanical behaviour of the stems placed in varus or valgus positions.
The study of both groups using DEXA at 5 years shows less proximal bone atrophy in the ABG-II Group, with an 8.7% improvement of the BMD [7, 8]. Therefore this stem improves the proximal transmission of loads. It has been proved that the stem's smaller proximal and distal diameters, in relation to the ABG-I, conserves a greater quantity of metaphyseal bone, taking into account that it is the biological factor which has most influence in the remodelling. Concerning the changes in the design, geometric modificaciton have proved to be more effective than material replacement.
This research was partially supported by a"Estudio del comportamiento mecánico de prótesis de cadera de apoyo metafisiario", grant funded by Stryker Iberia, S. L.
- Huiskes R, Weinans H, Dalstra M: Adaptative bone remodelling and biomechanical design considerations for noncemented total hip arthroplasty. Orthopedics 1989, 12: 1255–1267.Google Scholar
- Sychter CJ, Engh CA: The influence of clinical factor on periprosthetic bone remodelling. Clin Orthop 1996, 322: 285–292.Google Scholar
- Engh CA Jr, Young AM, Engh CA Sr, Hopper RH Jr: Clinical consequences of stress shielding after porous-coated total hip arthroplasty. Clin Orthop Relat Res 2003, 417: 157–163.Google Scholar
- Glassman AH, Bobyn JD, Tanzer M: New femoral designs: do they influence stress-shielding? Clin Orthop 2006, 453: 64–74. 10.1097/01.blo.0000246541.41951.20View ArticleGoogle Scholar
- Wick M, Lester DK: Radiological changes in second and third generation Zweymuller stems. J Bone Joint Sur Br 2004, 86(8):1108–14. 10.1302/0301-620X.86B8.14732View ArticleGoogle Scholar
- Herrera A, Canales V, Anderson J, García-Araujo C, Murcia-Mazón A, Tonino AJ: Seven to ten years follow up of an anatomic hip prosthesis. Clin Orthop 2004, 423: 129–137. 10.1097/01.blo.0000128973.73132.0bView ArticleGoogle Scholar
- Panisello JJ, Herrero L, Canales V, Herrera A, Martínez A, Mateo J: Long-Term Remodelling in Proximal Femur around a Hydroxyapatite-Coated Anatomic Stem. Ten Years Densitometric Follow-Up. J Arthroplasty 2008, 24: 56–64. 10.1016/j.arth.2007.12.017View ArticleGoogle Scholar
- Panisello JJ, Canales V, Herrero L, Herrera A, Mateo J, Caballero MJ: Changes in periprosthetic bone remodelling after redesigning an anatomic cementless stem. Int Orthop 2009, 33(2):373–9. 10.1007/s00264-007-0501-zView ArticleGoogle Scholar
- Gruen TA, McNeice GM, Amstutz HC: Modes of failure of cemented stem-type femoral components: a radiographic analysis of loosening. Clin Orthop RR 1979, 141: 17–27.Google Scholar
- Herrera A, Panisello JJ, Ibarz E, Cegoñino J, Puértolas JA, Gracia L: Long-term study of bone remodelling after femoral stem: A comparison between dexa and finite element simulation. J Biomech 2007, 40(16):3615–25. 10.1016/j.jbiomech.2007.06.008View ArticleGoogle Scholar
- I-DEAS 2009. [http://www.ugs.com/]
- ABAQUS 2009. [http://www.simulia.com/]
- Shirazi-Adl A, Dammak M, Paiement G: Experimental determination of friction characteristics at the trabecular bone/porous-coated metal interface in cementless implants. J Bio Mat Res 1993, 27: 167–175. 10.1002/jbm.820270205View ArticleGoogle Scholar
- Ashman RB, Rho JY: Elastic modulus of trabecular bone material. J Biomech 1988, 21: 177–181. 10.1016/0021-9290(88)90167-4View ArticleGoogle Scholar
- Ashman RB, Cowin SC, Van Buskirk WC, Rice JC: A continuous wave technique for the measurement of the elastic properties of cortical bone. J Biomech 1984, 17: 349–361. 10.1016/0021-9290(84)90029-0View ArticleGoogle Scholar
- Evans FG: The Mechanical Properties of Bone. Springfield, IL: ed., American Lecture Series; 1973:881.Google Scholar
- Ionescu I, Conway T, Schonning A, Almutairi M, Nicholson DW: Solid modeling and static finite element analysis of the human tibia. Sonesta Beach Resort in Key Biscayne, Florida, June. Summer Bioengineering Conference, 25–29, 2003 Google Scholar
- Jacobs CR: Numerical simulation of bone adaptation to mechanical loading. Dissertation for the degree of Doctor of Philosophy, Stanford University; 1994.Google Scholar
- MatWeb (Material Property Data) 2009. [http://www.matweb.com/]
- Meunier A, Riot O, Christel P, Katz JL, Sedel L: Inhomogeneities in anisotropic elastic constants of cortical bone. Ultrasonics Symposium 1989, 1015–1018.View ArticleGoogle Scholar
- Turner CH, Rho J, Takano Y, Tsui TY, Pharr GM: The elastic properties of trabecular and cortical bone tissues are similar: results from two microscopic measurement techniques. J Biomech 1999, 32: 437–441. 10.1016/S0021-9290(98)00177-8View ArticleGoogle Scholar
- Val BCH, Rahmy A, Grimm B, Heyligers I, Tonino A: Preoperative bone quality as a factor in dual-energy X-ray absorptiometry analysis comparing bone remodelling between two implant types. Int Orthop On line 2006.Google Scholar
- Kerner J, Huiskes R, van Lenthe GH, Weinans H, van Rietbergen B, Engh CA, Amis AA: Correlation between pre-operative periprosthetic BMD and post-operative bone loss in THA can be explained by strain-adaptative remodelling. J Biomech 1999, 32: 695–703. 10.1016/S0021-9290(99)00041-XView ArticleGoogle Scholar
- Turner AWL, Gillies RM, Sekel R, Morris P, bruce W, Walsh WR: Computational bone remodelling simulations and comparisons with DEXA results. J Orthop Res 2005, 23: 705–712. 10.1016/j.orthres.2005.02.002View ArticleGoogle Scholar
- Karachalios T, Tsatsaronis Ch, Efraimis G, Papadelis P, Lyritis G, Diakoumopoulos G: The long-term clinical relevance of calcar atrophy caused by stress shielding in total hip arthroplasty. J Arthroplasty 2004, 19: 469–475. 10.1016/j.arth.2003.12.081View ArticleGoogle Scholar
- Nishii T, Sugano N, Masuhara K, Shibuya T, Ochi T, Tamura S: Longitudinal evaluation of time related bone remodelling after cementless total hip arthroplasty. Clin Orthop Relat Res 1997, 339: 121–131. 10.1097/00003086-199706000-00017View ArticleGoogle Scholar
- Rietbergen B, Huiskes R: Load transfer and stress shielding of the Hydroxyapatite ABG hip. A Study of stem length and proximal fixation. J Arthroplasty 2001, 16: 55–63. 10.1054/arth.2001.28369View ArticleGoogle Scholar
- Senalp AZ, Kayabasi O, Kurtaran H: Static, dynamic and fatigue behaviour of newly designed stem shapes for hip prosthesis using finite element analysis. Mater Des 2007, 28: 1577–1583.View ArticleGoogle Scholar
- Bergmann G, Graichen F, Rohlmann A: Hip joint forces during walking and running, measured in two patients. J Biomech 1993, 26: 969–990. 10.1016/0021-9290(93)90058-MView ArticleGoogle Scholar
- Bergmann G, Deuretzbacher G, Heller M, Graichen F, Rohlmann A, Strauss J, Duda GN: Hip contact forces and gait patterns from routine activities. J Biomech 2001, 34: 859–871. 10.1016/S0021-9290(01)00040-9View ArticleGoogle Scholar
- Tonino AJ, Therin M, Doyle C: Hydroxyapatite coated femoral stems: Histology and histomorphometry around five components retrieved at postmortem. J Bone Joint Surg 1999, 81B: 148–54. 10.1302/0301-620X.81B1.8948View ArticleGoogle Scholar
- Gibbons CER, Davies AJ, Amis AA, Olearnik H, Parker BC, Scott JE: Periprosthetic bone mineral density changes with femoral components of differing design philosophy. In Orthop 2001, 25: 89–92.Google Scholar
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