Skip to main content
Journal of Experimental Orthopaedics
Download PDF
  • Original Paper
  • Open access
  • Published:

Superior bone fixation of conical compared with hemispherical trapezial cup design: an experimental radiostereometry study

Journal of Experimental Orthopaedics volume 10, Article number: 127 (2023) Cite this article

Abstract

Purpose

The most used cup designs for trapeziometacarpal (TMC) arthroplasty are of hemispherical and conical geometrical shape. Using a validated pig bone model, we compared the bone fixation using radiostereometry (RSA).

Methods

Twenty saddle-shaped pig forefoot bones were prepared with insertion of bone markers and reaming. Hemispherical Type T cups (Beznoska, Kladno, Czech Republic) (N = 10) and conical Moovis cups (Stryker, Pusignan, France) (N = 10) of 9-mm diameter were inserted press-fit. The bones were fixed in cement blocks for stability, and the cups were loaded in a motorized test stand. First, a low-pressure cyclic load test (0—150N) with 130 compression cycles was performed. Next, a push-in test of progressive loads with 50N increments (range: 150–900N) was applied until a visual change in cup position appeared. Cup migration was evaluated with RSA after every new load application. Cup failure was defined as total translation > 0.5 mm between two load applications.

Results

Both cup types tolerated a compression load of 450 N without failure. Beyond this load level, the total translation cup migration of mean 0.20 mm (95% CI 0.11; 0.30) for the Type T group was higher than mean 0.10 mm (95% CI 0.06; 0.15) of the Moovis group (p = 0.046). The Hazard ratio for failure was 0.52 (95% CI 0.12; 2.17) (p = 0.37), indicating that the risk of failure was two-fold higher in the Type T group.

Conclusion

We conclude that conical TMC cups have superior fixation as compared to hemispherical cups above a loading level of 450 N, which correspond to a 3.8 kg tip-pinch.

In a clinical perspective, based on the fixation strength of both cup types, it seems safe to allow light-load activities of daily living such as buttoning a shirt and using a key shortly after surgery and until sufficient osseointegration is achieved.

Background

Trapeziometacarpal arthroplasty is a treatment option for trapeziometacarpal (TMC) joint osteoarthritis (OA), which preserves thumb length and protect against secondary metacarpophalangeal joint hyperextension [8]. Recent publications show that TMC arthroplasty reduces pain, improves grip and pinch strength, and improves function as measured by patient reported outcome measures [7, 9, 25]. The first trapezial cup designs had early and frequent failure related to aseptic loosening with up to 44% failure at two years follow-up [17, 30]. Several cup designs and fixation methods including cementation, screw-fixation, and press-fit fixation have been introduced. Conical and hemispherical geometry design with cementless fixation has been continued and five to ten years survival rates have improved to 90.8 – 96% for hemispherical cups (Arpe cup, Zimmer Biomet, Warsaw, IN, USA, and Maiä cup, Groupe Lépine, Genay Cedex, France) [1, 5, 7, 12, 19, 32] and to 95 – 100% for conical cups (Moovis cup, Stryker, Pusignan, France and Ivory cup, Stryker, Kalamazoo, MI, USA) [13, 20, 25, 26].

For conical cups, the surface area and cup diameter have been shown to affect the primary mechanical stability and load tolerance after press-fit fixation in bone [28]. Considering the same cup diameter of conical cups and hemispherical cups, the surface area is smaller for hemispherical cups [28]. Therefore, the postoperative load tolerance until achievement of secondary osseointegration is likely higher for conical cups. Primary mechanical cup fixation is important for the achievement of later osseointegration and implant survival [21, 22, 24]. Radiostereometry (RSA) is a precise imaging method for the measurement of implant migration, and early implant migration has a high predictive value for longer-term fixation of hip and knee arthroplasty [18, 22, 23, 33]. RSA is a validated method for evaluation of cup fixation in TMC arthroplasty [15], which has been used for evaluation of prospective cup migration in clinical studies [16, 27] as well as for evaluation of primary mechanical cup fixation in an experimental pig bone model [14, 28].

The purpose of this study was to compare RSA measured migration of a press-fit hemispherical and a conical-shaped TMC cup in a pig bone model.

Methods

Pig bone model

We used the saddle-shaped bone from the forefoot of five to six-month-old Danish Landrace pigs. A total of 20 forefeet were included and randomly allocated to hemispherical (Type T) or conical (Moovis) cup in a 1:1 ratio. The forefeet were scanned by dual-energy x-ray absorptiometry (DXA) in a posterior-anterior position and the BMD was measured in the central part of the saddle-shaped bone [4] and reported as g/cm2. Thereafter, the saddle-shaped bones were dissected from the pig's forefeet and prepared for RSA with six 1-mm tantalum beads in the subchondral bone by use of a bead-injector (Kulkanon, Wennberg Finmek, Gunnilse, Sweden).

Implants

The Type T cup (Beznoska, Kladno, Czech Republic) is a cementless press-fit hemispherical cup made of Ti6Al4V alloy (ISO 5832–3) with 3 rim-fins and an external diameter of 9 mm (Fig. 1A). The surface is coated with a plasma-spray double layer of titanium and hydroxyapatite. The titanium coating thickness is 0.1‐0.2 mm with a grain size of 0.075–0.18 mm and a roughness of 100–200 μm (international norm: ASTM F1580‐07). The hydroxyapatite coating of 2(Ca5(Po4)3OH) is 0.04–0.08 mm in thickness with a grain size of 0.05–015 mm and a roughness of 50–100 μm (international norm: ISO 13779‐1:2008). The inner surface with a Ø7.30 mm is manufactured by machine and polished by hand (roughness 0.2 Ra). The polyethylene liner is made of compression-molded and machined-manufactured modified crosslinked ultra-high-molecular-weight polyethylene (UHMWPE) (ISO 5834–2) and is fixed with a click-lock in the cup. The head-neck segment is made of molybdenum alloy (ISO 5832–12) and the head size is 5 mm in diameter. The original instrumentation (alignment reamers and cutting reamers) as well as the recommended surgical technique was used. The alignment reamer had eight cutterhead blades and the hemispherical size Ø8 and Ø9 mm reamers had nine cutterhead blades (Fig. 1A). The reaming system was designed for 0.1 mm under-reaming of the cup diameter. The full reamer depth was similar to the external depth of the cups.

Fig. 1
figure 1

The design of A the hemispherical Type T cup and bone reamers and B the conical Moovis cup and bone reamers

Full size image

The Moovis cup (Stryker, Pusignan, France) is a cementless press-fit conical cup CNC machined from chrome-cobalt alloy with external measures of 9 mm diameter and a dept of 7 mm (Fig. 1B). The surface is coated with a plasma-spray double layer of titanium and hydroxyapatite. The titanium coating is 0.1 mm and the hydroxyapatite coating is 0.1 mm in thickness. The dual-mobility polyethylene insert is manufactured from UHMWPE and has an external diameter of 8.2 mm and a dept of 6 mm. The head-neck segment is made of chrome-cobalt and the head size is 5 mm in diameter. The original instrumentation as well as the recommended surgical technique was used. There were two Ø9 mm cutting reamers (one with four cutterhead blades and one with eight cutterhead blades) intended for line-to-line reaming of the cup diameter (Fig. 1B). The full reamer depth was 1 mm more than the external depth of the hydroxyapatite coated area of the cups.

Surgical technique

Type T cup

A k-wire was inserted in the center of the articulate surface of the saddle-shaped bone. An alignment reamer was used to level the cartilage surface to the cortical bone (Fig. 2A). Cutting reamers size Ø8 mm and Ø9 mm on a reaming drill were used for preparation of the implant cavity. The cup was inserted over the guidewire using the original impactor and a hammer, and the cup was advanced to the cortical surface in order to achieve press-fit rim-fixation (Fig. 2A).

Fig. 2
figure 2

The A + B bone reaming, C + D press-fit cup insertion in the pig bone, and E + F failure with visual cup displacement of the Type 2 cup (upper panel) and the Moovis cup (lower panel)

Full size image

Moovis cup

A k-wire was inserted in the center of the articulate surface of the saddle-shaped bone. The two cutting reamers size Ø9 mm on a reaming drill were used for preparation of the implant cavity (Fig. 2B). The k-wire was removed and the cup was inserted using the original impactor and a hammer. The cup was advanced to the bottom of the implant cavity (until no further advancement of the implant was felt/seen during impaction) obtaining a tight cortical press-fit rim-fixation and leaving the non-coated rim of the cup outside the cartilage (Fig. 2B).

Compression test

The set-up consisted of a Mark-10 motorized test stand ESM300 with a BGI SS200 controller (Swetest Instrument AB, Saltsjö-Boo, Sweden). A head-neck segment with a 5 mm head was mounted on the Mark-10 test stand and used to apply a compression load on the cup (Fig. 3A). For the Moovis cup, a dual-mobility polyethylene liner was mounted on the head-neck segment (Fig. 1B). For the Type T cup, the polyethylene liner was mounted in the cup (Fig. 1A). In this way, a centralized compression load of the cup into the saddle-shaped bone was performed. The load of the TMC joint was a combination of axial forces and horizontal forces [6]. In order to mimic the functional loading angle on the TMC cup in the natural TMC joint, the bones were rigidly fixed in separate blocks of bone cement (Heareus Palacos R + G) in a 20-degree angle on the horizontal plane (Fig. 2C + 2D) [14]. We performed two different compression tests on the cups (Fig. 4). First, a low-pressure cyclic load test (150N) was performed, which corresponds to a 15 kg load on the cup and a 1.25 kg tip-pinch. A force of 150N was not expected to result in any major force or migration of the cups, but the load simulated light-load repetitive activities of daily living [6, 29]. Second, a push-in test (150 – 900N) was performed, which corresponds to a max 92 kg load on the cup and a 7.6 kg tip-pinch [6]. A force of 900N was expected to challenge or exceed the primary mechanical cup fixation leading to cup migration or cup loosening [28].

Fig. 3
figure 3

A The motorized Mark-10 test stand mounted with a 5 mm head-neck segment to apply a compression load on the cup during testing. B The DR RSA set-up with two ceiling-mounted x-ray tubes used for recording stereo-radiographs of the cup and bone-markers

Full size image
Fig. 4
figure 4

Overview of the two-phased study flow with a low-pressure cyclic load test (0-150N) and a push-in test stress test (150-900N) and regular RSA imaging

Full size image

In the low-pressure cyclic load test 130 compression cycles with load-increase from 0 – 150N was performed. The down speed was 4 mm/min and the dwell time was 4 s at the 150N load.

The push-in test applied 2 compression cycles of progressive load with 50N increments (range: 150–900N). The down-speed was 4 mm/min and the dwell time was 1 s between each load cycle. The tests were similar to an earlier study of different TMC implants [14].

Radiostereometric Analysis (RSA)

Radiostereometric (RSA) imaging of the cups was performed at baseline, after the low-pressure cyclic load test, and repeated after every 150N load increment (300N, 450N, 600N, 750N, and 900N) (Fig. 4). The position of the cement-blocks with the bone-implant specimens was standardized in a radiolucent positioner at every RSA examination (Fig. 3B). The RSA set-up consisted of a direct digital stereo x-ray system (AdoraRSA suite; NRT, Aarhus, Denmark) with 2 ceiling-mounted x-ray tubes in vertical position with a 40-degree angulation between tubes (Fig. 3B). The source image distance (SID) between the tubes and detectors was 116 cm. Exposure settings were 66 kV, 200 mA, and 6.3 mAs. A wireless digital x-ray image detector (CXDI-801C; Canon, Tokyo, Japan) was slotted beneath a uniplanar Perspex hand calibration box (Medis Medical Imaging Systems BV, Leiden, the Netherlands). The resolution of the static images was 79 dpi. The RSA images were obtained as one DICOM file and converted to BMP images as the radiographs were split for RSA analysis.

Model-based RSA analysis

Model-based RSA version 4.2 (RSAcore, LUMC, Leiden, the Netherlands) was used for analysis of the RSA images for measurement of cup migration. Each RSA image was calibrated, which aligned the bone-marker model in all examinations. Reverse engineered cup models were created by laser scanning of real implants of the same size (RSAcore, Leiden, the Netherlands). The cup model was fitted to the contour of the implant in the RSA images with a pose error of 0.99 mm (SD 0.01) for Type T cups and 0.69 mm (SD 0.01) for Moovis cups (Fig. 3B). The migration of the cup model with respect to a rigid marker-model of the tantalum beads in the bone was given by the software. The coordinate system of the two cup designs was similar with the y-axis placed in the central axis of the cup and pointing through the dome. The cup migrations were expressed as translations along the orthogonal x-, y-, and z-axes with respect to the marker-model and with reference to the baseline examination. The total translation (TT) was calculated as TT = √(x2 + y2 + z2). Rotations were not estimated due to the rotational symmetry of the Moovis cup. There were no left–right side issues to take into account.

Radiostereometric precision

The RSA recordings were performed as double examinations for all cups at 150 N and at 750 N in order to evaluate precision. Precision was evaluated as cup migration between the double RSA recordings and reported as mean difference (systematic bias) with minimum and maximum values, and precision (SD of the mean differences × 1.96). Numbers for signed and absolute values were given.

Sample size

The sample size was based on a clinical RSA precision study examining migration of the conical shaped threaded Elektra cup in patients [15]. Using a standard deviation of 0.32 mm, power of 80, and alpha of 0.05, we estimated a sample size of n = 8 per group for the detection of a mean difference in TT migration of 0.5 mm [16, 22].

Data interpretation

Hansen and Stilling (2013) found a mean 0.19 mm TT with an upper 95% confidence interval of 0.5 mm for non-revised Electra cups in a clinical study. Based on these observations we defined a TT increase, between two compression tests, exceeding 0.5 mm as cup-loosening (failure). Cup migration along the x-, y-, and z-axes and TT until failure of the first cup (0 – 450N) was compared between groups, and cup migration until max load (0 – 900N) was displayed graphically. The maximum tolerated compression load (N) before the summed TT reached 0.5 mm, was assessed for all cups, compared between groups, and compared between failed and non-failed cups.

Statistical analysis

The hypothesis of no difference in translation (primary outcome: TT, secondary outcomes: x, y, z axes) between groups before the first cup failure (0N to 450N) was analyzed using a univariate repeated measurement analysis (mixed model), with compression load (N) and cup type as fixed effects, and implant number as random effects. We used pairwise group comparisons for each compression load (N) to describe differences. Unequal standard deviations and correlations of the cup-type groups were considered in the analyses. Normal distribution of the mixed-model residuals was evaluated with quantile–quantile plots.

Using a student’s independent two sample t-test (equal variance) the BMD of the saddle-shaped pig bones and the TT of failed and non-failed cups, was compared between cup groups. The normality of continuous data was inspected using frequency and probability plots (quantile–quantile plots). Continuous data was reported as means with 95% confidence intervals (95% CI). Categorical data between groups was compared with a chi-squared test. The cumulative rate of cup survival was estimated using the Kaplan–Meier method. The level of significance was set at p < 0.05.

Results

Demographics

One Moovis cup was excluded from all analyses because of an error in the compression test. We did not experience any fractures of the saddle-shaped pig bones during reaming and cup insertion, or during the compression testing.

Bone mineral density

The BMD was 0.43 g/cm2 (95% CI 0.38; 0.47) in the Type T group and 0.47 g/cm2 (95% CI 0.40; 0.53) in the Moovis group (p = 0.30).

Cup migration

The low-pressure cyclic loading test (0-150N) resulted in TT cup migration of 0.07 mm (95% CI 0.04; 0.09) for the Type T group and of 0.07 mm (95% CI 0.02; 0.12) for the Moovis group (p = 0.95).

During the push-in test, the first cup failures (defined as TT migration above 0.5 mm) between each compression test were seen at 600 N load in the Type T group and at 900 N load in the Moovis group. In the load-interval without failures (0-450N), TT cup migration was 0.20 mm (95% CI 0.11; 0.30) for the Type T group and 0.10 mm (95% CI 0.06; 0.15) for the Moovis group (p = 0.047). The signed cup translations (x, y, z) were similar between groups (p > 0.06) (Fig. 5).

Fig. 5
figure 5

Cup migration evaluated with radiostereometry shown as Total translation (TT) and signed migration along the x, y, and z axes for the Type T and Moovis cup groups

Full size image

At the final load (900N), 5 of 10 Type T cups and 3 of 9 Moovis cups had exceeded the migration failure limit of 0.5 mm TT between load tests (p = 0.46). The max TT translation for non-failed cups at 900N was 0.33 mm (95% CI 0.20; 0.46) for the Type T group and 0.23 mm (95% CI 0.09; 0.36) for the Moovis group (p = 0.27). The max TT translation for failed cups (TT > 0.5 mm between load tests) was 1.75 mm (95% CI 0.75; 2.75) for the Type T group and 1.44 mm (95% CI 0.65; 2.23) for the Moovis group (p = 0.56). Groups combined, the maximum TT migration was 0.24 mm (95% CI 0.11; 0.38) in the non-failure group (n = 11) and 1.28 mm (95% CI 0.88; 1.70) in the failure group (n = 8) (p = 0.0001).

Migration pattern

Overall, the Type T group migrated more along all three orthogonal axes from 0 to 900N as compared with the Moovis group (Fig. 5). By visual assessment of the graphs, the Type T group migration started already at 450N, whereas the Moovis group was stable until 750N. Visually, this presented as a small cup tilt followed by subsidence and horizontal translation for the Type T cups. The Moovis cups had a similar migration pattern during failure (Fig. 5).

For the Type T group, the migration pattern for the whole loading test showed a maximum mean 0.26 mm (95% CI -0.38; -0.14) x-translation, 0.76 mm (95% CI 0.46; 1.06) y-translation, and -0.52 mm (95% CI -0.76; -0.28) z-translation. For the Moovis group, the migration pattern for the whole loading test showed a maximum mean -0.02 mm (95% CI -0.05; 0.01) x-translation, 0.45 mm (95% CI 0.32; 0.58) y-translation, and -0.39 mm (95% CI -0.55; -0.23) z-translation.

Cup survival

The Kaplan–Meier cumulative survival estimate at 900 N, was 50% (95% CI 18; 75) in the Type T group and 67% (95% CI 28; 88) in the Moovis group (Fig. 6). The risk difference was 17% (95% CI -27; 60) and in favor of the Moovis group (p = 0.45). The Hazard ratio for failure was 0.52 (95% CI 0.12; 2.17) (p = 0.37), indicating that the risk of failure was two-fold higher in the Type T group.

Fig. 6
figure 6

Kaplan–Meier cumulative survival plot for cup failure (TT migration > 0.5 mm)

Full size image

RSA precision

There was no systematic bias (mean difference) in TT and no difference in TT precision between the Type T group and the Moovis group (p > 0.71). The TT mean difference of the double examination stereo-radiographs was 0.031 mm and the precision was mean 0.066 mm (Table 1).

Table 1 Repeatability of cup migration as signed and absolute values from RSA double-examinations (n = 38 double examinations)
Full size table

Discussion

The focus of this experimental study was to evaluate mechanical TMC cup fixation in the saddle shaped bone of a pig bone model. The study showed that beyond a compression load of 450 N the hemispherical Type T cup group had higher cup migration, and a two-fold higher risk of failure, as compared with the conical Moovis cup group.

There may be several explanations to these findings. The surface area of a 9 mm conical Moovis cup is 31% larger than for a 9 mm hemispherical cup. Thus, conical cups have better bone support at the time of primary cup fixation. Furthermore, for a larger cup diameter, the surface area of the Moovis cups has a greater percentage increase compared to the Type T cup. An experimental study of the conical Konos cup (Beznoska, Kladno, Czech Republic) inserted with cortical bone rim fixation showed that the risk difference for failure was 63% in favor of 10 mm cups compared to 9 mm cups [28].

The center of rotation in ball-and-socket cup designs defines the resultant force vector on the cup. For both the Moovis cup and the Type T cup the rotation center is level with the cup base. The hemispherical Type T cup is inserted level to the cortical bone surface, whereas the conical Moovis cup is designed to protrude slightly from the cortical bone surface. With a center of rotation outside the cortical bone surface the inclined resultant force vector increases in magnitude, which may cause eccentric loading and jeopardize mechanical bone fixation. Finite element analysis has shown that conical cups with a center of rotation at the bone surface deliver less stress to the cortical bone rim during angular loading of 30° compared with conical cups with a center of rotation that is above the bone surface [30]. The extrinsic center of rotation was probably the main cause of early failures with the Motec (Swemac AB, Linköbing, Sweden) cup design [30, 31].

In the present study, the TT before failure of the first cup (450N) was a mean of 0.20 mm for the Type T group and a mean of 0.10 mm for the Moovis group. In comparison, a recent similar experimental study of the conical Konos cup reported a TT of mean 0.23 mm at 450N [28].

A load of 450N resembles a hand grip of 45.9 kg and a tip-pinch of 3.8 kg [6]. In a 2-year follow-up of 200 patients operated with the Moovis cup, the hand grip for men and women combined was reported to mean 29 kg and none had grip strength above 45.9 kg [9]. In a population with osteoarthritis of the hand, the finger forces used during activities of daily living that primarily used the thumb and index finger in a precision grip were studied. The maximum force applied to the thumb ranged from 7.9 N (± 1.8) (approximately 1 kg) during a shirt button task to 30.7 N (± 3.7) (approximately 3.5 kg) during plug-in of a toaster [29]. Thus, a 450N load seems to be a clinically relevant upper limit for testing primary mechanical cup fixation.

Load- and shear-stresses at the implant-bone interface may not be the same with different cup designs. In the present study, the migration pattern on the graphical presentations of the 0 – 900N push-in test showed more subsidence of Type T cups at increasing loads as compared with Moovis cups. Furthermore, Type T cups translated horizontally to the articular bone surface along the z-axis indicating a failure pattern with loss of cortical rim-fixation and peri-prosthetic bone support. Visually, this presented as a cup-tilt followed by subsidence and horizontal translation. For the Moovis cups, the failure pattern was mainly subsidence with slight horizontal translation, but the migration leading to failure started at higher compression loads. The advantage of the Moovis cup design is that the geometry allows for some subsidence without loss of cortical rim-fixation. Perhaps, the cortical rim-fixation may even improve with loading of the conical Moovis cup during daily activities. The disadvantage of the conical cup shape is the risk of intra-operative stress fracture upon impaction of the cup [9]. Yet, there is also a risk of intra-operative fracture with press-fit hemispherical TMC cup designs [10, 12]. Intra-operative fracture as well as cup survival may be related to bone quality. In hip replacement surgery both stem and cup migration, as a predictor of implant survival, is higher in patients with low systemic bone mineral density (T-score < -1) [2, 11]. Bone antiresorptive treatment with RANK-L inhibitors (Denosumab) increase the periprosthetic bone mineral density in clinically relevant regions of the proximal femur, but the treatment response is not associated with a reduction in stem migration [3]. Coating roughness and porosity may also affect implants' primary mechanical fixation, and super-coatings such as hydroxyapatite have been optimized for years to aid osseointegration. However, in the present study, both cup types were coated with a similar plasma-spray double layer of titanium and hydroxyapatite.

The study was performed in a pig bone model and has natural limitations i.e., primary mechanical cup fixation cannot be directly translated to humans and cannot predict long-term cup fixation and survival. However, it benefits from a standardized setting utilizing a highly precise and validated quantitative imaging and analysis method. Further, the load application on the cups can be argued to have a high clinical relevance.

We conclude that conical TMC cups have superior fixation as compared with hemispherical cups above a loading level of 450 N, which corresponds to a 3.8 kg tip-pinch. In a clinical perspective, based on the fixation strength of both cup types, it seems safe to allow light-load activities of daily living such as buttoning a shirt and using a key shortly after surgery and until sufficient osseointegration is achieved.

Availability of data and materials

The datasets used and/or analyzed during the current study are available from the corresponding author on reasonable request.

Abbreviations

BMD:

Bone mineral density

CNC:

Computer Numerical Control

CI:

Confidence interval

DXA:

Dual-energy x-ray absorptiometry

OA:

Osteoarthritis

RSA:

Radiostereometry

TMC:

Trapeziometacarpal

TT:

Total translation

Type T:

Hemispherical shaped cup type

Moovis:

Conical shaped cup type

UHMWPE:

Ultra-high-molecular-weight polyethylene

References

  1. Andrzejewski A, Ledoux P (2019) Maia trapeziometacarpal joint arthroplasty: Survival and clinical outcomes at 5 years’ follow-up. Hand Surg Rehabil 38:169–173

    Article  CAS  PubMed  Google Scholar 

  2. Aro HT, Alm JJ, Moritz N, Makinen TJ, Lankinen P (2012) Low BMD affects initial stability and delays stem osseointegration in cementless total hip arthroplasty in women: a 2-year RSA study of 39 patients. Acta Orthop 83:107–114

    Article  PubMed  PubMed Central  Google Scholar 

  3. Aro HT, Nazari-Farsani S, Vuopio M, Loyttyniemi E, Mattila K (2019) Effect of Denosumab on Femoral Periprosthetic BMD and early femoral stem subsidence in postmenopausal women undergoing cementless total hip arthroplasty. JBMR Plus 3(10):e10217

    Article  PubMed  PubMed Central  Google Scholar 

  4. Breddam Mosegaard S, Breddam Mosegaard K, Bouteldja N, Baek Hansen T, Stilling M (2018) Trapezium Bone Density-A comparison of measurements by DXA and CT. J Funct Biomater 9(1):1–8

    Article  Google Scholar 

  5. Bricout M, Rezzouk J (2016) Complications and failures of the trapeziometacarpal Maia prosthesis: A series of 156 cases. Hand Surg Rehabil 35:190–198

    Article  CAS  PubMed  Google Scholar 

  6. Cooney WP 3rd, Chao EY (1977) Biomechanical analysis of static forces in the thumb during hand function. J Bone Joint Surg Am 59:27–36

    Article  PubMed  Google Scholar 

  7. Cootjans K, Vanhaecke J, Dezillie M, Barth J, Pottel H, Stockmans F (2017) Joint survival analysis and clinical outcome of total joint arthroplasties with the ARPE Implant in the treatment of trapeziometacarpal osteoarthritis with a minimal follow-up of 5 years. J Hand Surg Am 42:630–638

    Article  PubMed  Google Scholar 

  8. Degeorge B, Dagneaux L, Andrin J, Lazerges C, Coulet B, Chammas M (2018) Do trapeziometacarpal prosthesis provide better metacarpophalangeal stability than trapeziectomy and ligamentoplasty? Orthop Traumatol Surg Res 104:1095–1100

    Article  PubMed  Google Scholar 

  9. Dremstrup L, Thillemann JK, Kirkeby L, Larsen LP, Hansen TB, Stilling M (2021) Two-year results of the Moovis trapeziometacarpal joint arthroplasty with focus on early complications. J Hand Surg Eur 46:131–140

    Article  Google Scholar 

  10. Dumartinet-Gibaud R, Bigorre N, Raimbeau G, Jeudy J, Saint Cast Y (2020) Arpe total joint arthroplasty for trapeziometacarpal osteoarthritis: 80 thumbs in 63 patients with a minimum of 10 years follow-up. J Hand Surg Eur 45:465–469

    Article  Google Scholar 

  11. Finnila S, Moritz N, Svedstro ME, Alm JJ, Aro HT (2016) Increased migration of uncemented acetabular cups in female total hip arthroplasty patients with low systemic bone mineral density. A 2-year RSA and 8-year radiographic follow-up study of 34 patients. Acta Orthop 87:48–54

    Article  PubMed  Google Scholar 

  12. Gomez-Garrido D, Trivino-Mayoral V, Delgado-Alcala V, Cervera-Irimia J, Medina-Lorca M, Sanchez-Sanchez F et al (2019) Five year long term results of total joint arthroplasties in the treatment of trapeziometacarpal osteoarthritis. Acta Biomed 90:451–456

    PubMed  PubMed Central  Google Scholar 

  13. Goubau JF, Goorens CK, Van Hoonacker P, Berghs B, Kerckhove D, Scheerlinck T (2013) Clinical and radiological outcomes of the Ivory arthroplasty for trapeziometacarpal joint osteoarthritis with a minimum of 5 years of follow-up: a prospective single-centre cohort study. J Hand Surg Eur 38:866–874

    Article  CAS  Google Scholar 

  14. Hansen TB, Hengst D, Mortensen J, Amstrup AL (2011) Fixation of trapezial implants in a trapeziometacarpal total joint prosthesis tested in a model of porcine bone. J Plast Surg Hand Surg 45:263–266

    Article  PubMed  Google Scholar 

  15. Hansen TB, Larsen K, Bjergelund L, Stilling M (2010) Trapeziometacarpal joint implants can be evaluated by roentgen stereophotogrammetric analysis. J Hand Surg Eur 35:480–485

    Article  CAS  Google Scholar 

  16. Hansen TB, Stilling M (2013) Equally good fixation of cemented and uncemented cups in total trapeziometacarpal joint prostheses. A randomized clinical RSA study with 2-year follow-up. Acta Orthop 84:98–105

    Article  PubMed  PubMed Central  Google Scholar 

  17. Hansen TB, Vainorius D (2008) High loosening rate of the Moje Acamo prosthesis for treating osteoarthritis of the trapeziometacarpal joint. J Hand Surg Eur 33:571–574

    Article  CAS  Google Scholar 

  18. Karrholm J, Borssen B, Lowenhielm G, Snorrason F (1994) Does Early Micromotion of Femoral Stem Prostheses Matter - 4–7-Year Stereoradiographic Follow-up of 84 Cemented Prostheses. J Bone Joint Surg Br 76b:912–917

    Article  Google Scholar 

  19. Martin-Ferrero M (2014) Ten-year long-term results of total joint arthroplasties with ARPE(R) implant in the treatment of trapeziometacarpal osteoarthritis. J Hand Surg Eur 39:826–832

    Article  CAS  Google Scholar 

  20. Martins A, Charbonnel S, Lecomte F, Athlani L (2020) The Moovis(R) implant for trapeziometacarpal osteoarthritis: results after 2 to 6 years. J Hand Surg Eur 45:477–482

    Article  Google Scholar 

  21. Nelissen RG, Pijls BG, Karrholm J, Malchau H, Nieuwenhuijse MJ, Valstar ER (2011) RSA and registries: the quest for phased introduction of new implants. J Bone Joint Surg Am 93(Suppl 3):62–65

    Article  PubMed  Google Scholar 

  22. Pijls BG, Valstar ER, Nouta KA, Plevier JWM, Fiocco M, Middeldorp S, Nelissen RGHH (2012) Early migration of tibial components is associated with late revision: a systematic review and meta-analysis of 21,000 knee arthroplasties. Acta Orthop 83:614–624

    Article  PubMed  PubMed Central  Google Scholar 

  23. Ryd L, Albrektsson BEJ, Carlsson L, Dansgard F, Herberts P, Lindstrand A, Regnér L, Toksvig-Larsen S (1995) Roentgen Stereophotogrammetric Analysis as a Predictor of Mechanical Loosening of Knee Prostheses. J Bone Joint Surg Br 77b:377–383

    Article  Google Scholar 

  24. Soballe K, Hansen ES, H BR, Jorgensen PH, Bunger C (1992) Tissue ingrowth into titanium and hydroxyapatite-coated implants during stable and unstable mechanical conditions. J Orthop Res 10:285–299

    Article  CAS  PubMed  Google Scholar 

  25. Tchurukdichian A, Gerenton B, Moris V, See LA, Stivala A, Guillier D (2021) Outcomes of double-mobility prosthesis in trapeziometacarpal joint arthritis with a minimal 3 years of follow-up: an advantage for implant stability. Hand (NY) 16:368–374

    Article  Google Scholar 

  26. Tchurukdichian A, Guillier D, Moris V, See LA, Macheboeuf Y (2020) Results of 110 IVORY(R) prostheses for trapeziometacarpal osteoarthritis with a minimum follow-up of 10 years. J Hand Surg Eur 45:458–464

    Article  Google Scholar 

  27. Ten Brinke B, Beumer A, Koenraadt KLM, Eygendaal D, Kraan GA, Mathijssen NMC (2017) The accuracy and precision of radiostereometric analysis in upper limb arthroplasty. Acta Orthop 88:320–325

    Article  PubMed  PubMed Central  Google Scholar 

  28. Thillemann JK, Dremstrup L, Hansen TB, Stilling M (2021) The mechanical fixation of a cementless conical cup in cortical versus cancellous trapezial bone: an experimental study. J Hand Surg Eur 46:146–153

    Article  Google Scholar 

  29. Riddle M, MacDermid J, Robinson S, Szekers M, Ferreira L, Lalone E (2020) Evaluation of individual finger forces during activities of daily living in healthy individuals and those with hand arthritis. J Hand Therapy 33:188–197

    Article  Google Scholar 

  30. Thillemann JK, Thillemann TM, Munk B, Kroner K (2016) High revision rates with the metal-on-metal Motec carpometacarpal joint prosthesis. J Hand Surg Eur 41:322–327

    Article  CAS  Google Scholar 

  31. Thorkildsen R, Theodorsson J, Mellgren M, Rokkum M (2013) Comparison of two uncemented trapezio-metacarpal cups: a finite element study. Hand Surg 18:221–228

    Article  CAS  PubMed  Google Scholar 

  32. Toffoli A, Teissier J (2017) MAIA Trapeziometacarpal joint arthroplasty: clinical and radiological outcomes of 80 patients with more than 6 years of Follow-Up. J Hand Surg Am 42:831–838

    Article  Google Scholar 

  33. Valstar ER, Gill R, Ryd L, Flivik G, Borlin N, Karrholm J (2005) Guidelines for standardization of radiostereometry (RSA) of implants. Acta Orthop 76:563–572

    Article  PubMed  Google Scholar 

Download references

Acknowledgements

We would like to thank Anne Dorthe Riedel, from Department of Orthopaedics, Gødstrup Hospital, Denmark for her valued help with analysis of the radiostereometric images, and Lars Lindgren, from Department of Radiology, Aarhus University Hospital, for his professional help with photos.

Funding

Not applicable.

Author information

Authors and Affiliations

  1. Department of Orthopaedic Surgery, Aarhus University Hospital, Palle Juul-Jensens Boulevard 165 J801, DK- 8200, Aarhus N, Denmark

    Maiken Stilling & Janni Kjærgaard Thillemann

  2. Department of Clinical Medicine, Aarhus University, Aarhus N, Denmark

    Maiken Stilling, Torben Bæk Hansen & Janni Kjærgaard Thillemann

  3. AutoRSA Research Group, Orthopaedic Research Unit, Aarhus University Hospital, Aarhus N, Denmark

    Maiken Stilling & Janni Kjærgaard Thillemann

  4. Department of Orthopaedics, University Clinic for Hand, Hip and Knee Surgery, Gødstrup Hospital, Herning, Denmark

    Maiken Stilling, Lene Dremstrup, Torben Bæk Hansen & Janni Kjærgaard Thillemann

Authors
  1. Maiken Stilling
    View author publications

    You can also search for this author in PubMed Google Scholar

  2. Lene Dremstrup
    View author publications

    You can also search for this author in PubMed Google Scholar

  3. Torben Bæk Hansen
    View author publications

    You can also search for this author in PubMed Google Scholar

  4. Janni Kjærgaard Thillemann
    View author publications

    You can also search for this author in PubMed Google Scholar

Contributions

JKT contributed to acquisition of data, performed the data analysis and data interpretation, and writing the first draft of the manuscript. LD contributed to research design, acquisition of data, and data interpretation. TBH contributed to research design and data interpretation. MS contributed to research design, acquisition, and interpretation of data, and writing the first draft of the manuscript. All authors revised and approved the final version of the manuscript.

Corresponding author

Correspondence to Maiken Stilling.

Ethics declarations

Ethics approval and consent to participate

Not applicable.

Consent for publication

Not applicable.

Competing interests

The authors declare that they have no competing interests.

Additional information

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Rights and permissions

Open Access This article is licensed under a Creative Commons Attribution 4.0 International License, which permits use, sharing, adaptation, distribution and reproduction in any medium or format, as long as you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons licence, and indicate if changes were made. The images or other third party material in this article are included in the article's Creative Commons licence, unless indicated otherwise in a credit line to the material. If material is not included in the article's Creative Commons licence and your intended use is not permitted by statutory regulation or exceeds the permitted use, you will need to obtain permission directly from the copyright holder. To view a copy of this licence, visit http://creativecommons.org/licenses/by/4.0/.

Reprints and permissions

About this article

Check for updates. Verify currency and authenticity via CrossMark

Cite this article

Stilling, M., Dremstrup, L., Hansen, T.B. et al. Superior bone fixation of conical compared with hemispherical trapezial cup design: an experimental radiostereometry study. J EXP ORTOP 10, 127 (2023). https://doi.org/10.1186/s40634-023-00692-y

Download citation

  • Received:

  • Accepted:

  • Published:

  • DOI: https://doi.org/10.1186/s40634-023-00692-y

Keywords