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We evaluated site-specific skeletal adaptation to loading during growth,comparing radius (RAD) and femoral neck (FN) DXA scans in young female gymnasts (GYM) and non-gymnasts (NON).
Subjects from an ongoing longitudinal study (8-26 yrs old) underwent annual DXA scans (proximal femur, forearm, total body) and anthropometry, completing maturity and physical activity questionnaires. This cross-sectional analysis used the most recent data meeting the following criteria: gynecological age ≤2.5 yrs post-menarche; GYM annual mean gymnastic exposure ≥5.0 h/wk in the prior year. Bone geometric and strength indices were derived from scans for 173 subjects (8-17 yrs old) via hip structural analysis (femoral narrow neck, NN) and similar radius formulae (1/3 and Ultradistal (UD)). Maturity was coded as M1 (Tanner I breast), M2 (pre-menarche, ≥Tanner II breast) or M3 (post-menarche). ANOVA and chi square compared descriptive data. Two factor ANCOVA adjusted for age, height, total body non-bone lean mass and percent body fat; significance was tested for main effects and interactions between gymnastic exposure and maturity.
At the distal radius, GYM means were significantly greater than NON means for all variables (p<0.05). At the proximal femur, GYM exhibited narrower periosteal and endosteal dimensions, but greater indices of cortical thickness, BMC, aBMD and section modulus, with lower buckling ratio (p <0.05). However, significant interactions between maturity and loading were detected for the following: 1) FN bone mineral content (BMC), NN buckling ratio (GYM BMC advantages only in M1 and M3; for BMC and buckling ratio, M1 advantages were greatest; 2) 1/3 radius BMC, width, endosteal diameter, cortical cross-sectional area, section modulus (GYM advantages primarily post-menarche); 3) UD radius BMC and axial compressive strength (GYM advantages were larger with greater maturity, greatest post-menarche).
Maturity-specific comparisons suggested site-specific skeletal adaptation to loading during growth, with greater advantages at the radius versus the proximal femur. At the radius, GYM advantages included greater bone width, cortical cross-sectional area and cortical thickness; in contrast, at the femoral neck, GYM bone tissue cross-sectional area and cortical thickness were greater, but bone width was narrower than in NON. Future longitudinal analyses will evaluate putative maturity-specific differences.
The forearm and hip are major sites of osteoporotic fracture, together contributing over one third of the U.S. total (297,000 hip; 397,000 forearm). Furthermore, the distal radius is a common fracture site throughout life, with a peak in incidence occurring around the time of peak height velocity [2,3]. Thus, improvement of proximal femur and radius skeletal strength through non-pharmacological means is a vital strategy for reduction of the population fracture burden. Optimal physical activity exposure during growth may accomplish this aim, yielding long term bone strength benefits.
Supporting this premise, our group has published prospective, longitudinal evidence that gymnastics exposure during growth is associated with elevated DXA (dual X-ray absorptiometry) areal bone mineral density (aBMD), bone mineral content (BMC) and bone projected area (Area) at the distal radius/forearm, indicating persistent skeletal strength benefits at this important site [4,5]. The extreme model of artistic gymnastics is associated with uniquely exaggerated loads at both the non-dominant radius and the lower extremity [6-8]. Thus, observational studies of the gymnastic loading model provide the opportunity to evaluate skeletal adaptation to loading via site-specific DXA indices of bone geometry, density and associated theoretical skeletal strength at both the radius and the proximal femur.
Although cross-sectional studies have reported advantages in standard DXA outcomes for gymnasts (GYM) compared to non-gymnasts (NON) [9-14], few studies have evaluated indices of bone geometry and strength. Most bone geometric studies in women exposed to gymnastics have been performed at the forearm, often reporting greater indices of total bone size and strength in GYM and ex-GYM than NON [8, 15-24]. Although numerous studies have reported greater femoral neck aBMD in GYM than NON, to our knowledge, only two studies have specifically evaluated indices of femoral neck geometry and strength [25-26]. Both studies reported greater indices of bone strength but lower sub-periosteal width in GYM than NON, using hip structural analysis (HSA) [25-26]; one other study has reported lower femoral neck projected area in GYM versus NON . We are not aware of any published studies that have compared indices of bone geometry and strength at these two distinct sites, evaluating the effects of loading at both the forearm and the proximal femur, while accounting for variation in physical maturity.
This paucity of evidence limits our understanding of bone properties in GYM compared to NON, as available evidence is comprised of results from a variety of different methodologies, physical maturity groupings, and skeletal sites . Therefore, to address shortcomings in current knowledge, we evaluated site-specific skeletal adaptation to loading during growth, comparing radius (RAD) and proximal femur DXA scans in young female GYM versus NON, accounting for physical maturity variation from pre-puberty through post-menarche (Tanner breast stages I through V). We evaluated standard DXA outcomes of aBMD, BMC and projected area, as well as DXA-derived indices of bone geometry and strength [28-29]. We tested three related hypotheses, based upon existing literature: 1) GYM exhibit significant advantages in indices of bone mass, geometry, areal density and strength for both the radius and the femoral neck; 2) differences are of greater magnitude at the non-dominant distal radius than at the femoral neck; 3) although GYM exhibit advantages in theoretical bone strength at both sites, GYM periosteal width is greater at the radius and narrower at the femoral narrow neck.
In accordance with the Declaration of Helsinki and with the approval of our Institutional Review Board, prior to participation, subjects provided written, informed consent or assent with parental consent, as appropriate based on subject age. Subjects were enrolled in 3 separate cohorts, with GYM recruited from local gymnastic schools and NON recruited from local private schools, investigator contacts and University newletters: Cohort 1, 1997-8 (initial NON n= 25, GYM n= 55; current analysis: NON n= 25, GYM n= 50.); Cohort 2, 2002-2003 (initial NON n= 25, GYM n= 15; current analysis: NON n= 23, GYM n= 14); Cohort 3, 2008-2009 (initial NON n=30, GYM n= 50; current analysis: NON n=29, GYM n= 32). Numbers were lower in this analysis than at initial enrollment due to failure to meet gymnastic exposure criteria or incomplete data for focal variables.
Participants from our ongoing longitudinal study (8-26 yrs old) underwent annual DXA scans (proximal femur, forearm, total body). On a semi-annual basis, height, weight and waist circumference were measured; calendar-based physical activity questionnaires and maturity questionnaires were completed . The latter yielded self-reported Tanner breast and pubic stages, date of menarche, and subsequent gynecological age (years post-menarche). This cross-sectional analysis used the most recent complete data for which subjects exhibited a gynecological age no greater than 2.5 yrs. GYM were included if they had annual mean gymnastic exposure for the year prior to the DXA scan greater than or equal to 5.0 hours per week; in cases where subjects had multiple valid years of “GYM” data, the latest year with the most consistent training levels was used (to alleviate the possible influence of de-training effects related to injuries/illness).
Due to the cross-sectional nature of this analysis, we cannot determine causal relationships between factors and skeletal development within individuals across time. In this study, we will refer to the statistical “effects” of loading, estrogen exposure and their interaction as suggested by the results of cross-sectional comparisons.
We used annual mean gymnastic exposure for the year prior to the DXA session as our metric of gymnastic exposure dose (GYMHRS, h/wk), in part, because GYMHRS was the most reliably acquired data. GYMHRS was either recorded prospectively on a training calendar (early years Cohort 1) or recorded at measurement sessions to summarize the preceding 6-12 months (later years, Cohort 1; Cohorts 2 and 3). In contrast, age at training initiation and long-term training history were recalled up to 15 years post-hoc. Furthermore, within and between individuals, training intensity between training initiation and the focal DXA varied markedly (e.g. < 2 h/wk for 4 years, increasing to 12 h/wk over 3 subsequent years versus >8 h/wk within the 1st year training). Thus, GYMHRS was employed to minimize recall bias.
NON were not sedentary controls; they participated in a variety of physical activities, including <2 h/wk of gymnastics training (in a few cases). Subjects who exceeded an average of 2 hours per week of gymnastics over the prior year, but did not achieve 5.0 h/wk, were excluded from analysis. This exposure contrast has been associated with significant differences in DXA and peripheral quantitative computed tomography (pQCT) outcomes in related samples [19, 20].
Menarche status is known to be influential in skeletal development and loading associations [4, 5, 28], but distinctions between pre-pubertal, pubertal pre-menarcheal and post-menarcheal subjects have not been evaluated in a study on gymnastic loading. Accordingly, physical maturity status was evaluated in two ways: 1) maturity level (MAT) was coded as M1 (pre-menarche, Tanner breast stage I (all Tanner pubic stage I, except n=2 Tanner pubic II)), M2 (pre-menarche, Tanner breast stage II or greater) or M3 (post-menarche); 2) more standard analyses based on menarche status (MEN) contrasted differences pre-menarche versus post-menarche. In this manner, we hoped to distinguish between estrogen exposure levels without subjecting participants to invasive testing.
DXA scans of the left proximal femur, non-dominant forearm and total body were performed over a period from 1998 to 2010 using a single Hologic QDR4500W DXA scanner (94%), with a few exceptions performed on a cross-calibrated Discovery A scanner (6%, all from Cohort 3)(outcomes: Table 1a.--c.).c.). The vast majority of scans were performed by the study’s main technician (C.R., 2002-2010). All scans were reanalyzed by a single investigator (JD) using Apex software (Hologic Discovery A, software v.12.7.3, Waltham, MA, USA). Proximal femur and forearm results included standard aBMD, BMC and projected area for the femoral neck (FN; NN, narrow neck) and distal radius (RAD, 1/3 and ultradistal (UD) regions of interest). Total body DXA scans provided body composition data (percent body fat (PBF), total body non-bone lean mass (nbFFM)). As published previously, for the radius, non-standard positioning placed the edge of the analysis box distal to the distal radial articular cartilage but proximal to the carpal bones [5,28]. This key practice maximizes congruence of RAD regions of interest within and between individuals, allowing comparison of data from forearm scans exhibiting different ulnar variances [5,28].
FN bone geometric and strength indices were calculated using the manufacturer’s HSA program (direct computer output), with the NN box positioned at the narrowest portion of the FN. Similar formulae were used to calculate DXA-derived indices of RAD bone geometry and strength using simplified geometric models (1/3 and UD, modified for UD RAD) [28,30]. At the proximal femur, FN and NN BMC, Area and aBMD results were corrected for fan beam magnification error . Uncorrected and corrected ANCOVA results were very similar; corrected data are depicted graphically and in Table 2 (uncorrected data are presented only in Table 1c and Table 3). Redundant data are not presented (Width is derived from Area, so 1/3 Area, UD Area, FN Area are not presented; NN aBMD results are nearly identical to FN aBMD results, as the regions of interest usually overlap).
Coefficients of variation (CVs) for RAD and FN variables were calculated using duplicate scans of 23 middle-aged females. At both 1/3 and UD RAD, CVs were <1% for projected Area (and width), BMC and aBMD, as was the CV for 1/3 cCSA. For all other variables, CVs were <3%, with 3 exceptions: NN buckling ratio (BR, 3.8%), NN section modulus (Z, 7.0%) and NN cross-sectional moment of inertia (CSMI, 8.7%). Aside from NNZ and NNCSMI, our CVs were lower than or similar to those reported in other studies using FN and HSA data [32,33].
Based upon Tanner stage I/II comparisons , we projected that a minimum sample size of 17 subjects per cell would be necessary to detect significant FN differences in GYM versus NON (power ≥ 0.80). Based upon comparisons of standard and DXA-derived RAD outcomes at various maturity stages [4,18], projected minimum sample size ranged from 5 to 20. Accordingly, for all sites, we determined that 6 activity/maturity cells of at least 20 subjects should be adequate to evaluate the statistical effects of gymnastic loading exposure, maturity level (MAT) and interactions between them (latter of unknown effect size).
Analysis of variance (ANOVA) and chi square were used to compare descriptive data. As all variables were normally distributed, Pearson correlations were used to evaluate associations between potentially influential variables and bone outcomes. Two factor analysis of covariance (ANCOVA) adjusted for age, height, tbFFM and PBF. In this manner, we tested the significance of main effects for GYM status and MAT (M1, M2, M3) and evaluated the interaction between them (GYM status × MAT). Factors and covariates were kept in the model regardless of significance, to account for their potential influence upon the GYM status main effect. Additional analyses were performed for direct comparison of our FN results to the literature, adjusting for height and weight, and evaluating menarche status (MEN, pre-vs. post-menarche), GYM status and the interaction between them (GYM status × MEN) [25,26].
Within the GYM subgroup, we used linear regression models to evaluate the effects of gymnastics exposure dose over the year prior to the DXA scans (GYMHRS, h/wk) as a continuous variable, entering the following, in order: Model 1-age, nbFFM, PBF, MEN, GYMHRS and GYMHRS × MEN; Model 2- age, nbFFM, PBF, MAT (M1, M2, M3), GYMHRS and GYMHRS × MAT. Both nbFFM and GYMHRS were forced into the model, regardless of significance. In the event that GYMHRS was not a significant predictor using the nbFFM models, an analogous model was evaluated, substituting height for nbFFM. Aside from GYMHRS and nbFFM, variables were removed if p> 0.05 or their inclusion generated variance inflation factors (VIF) greater than 5.0. For all analyses, alpha = 0.05.
Data for 173 subjects were analyzed. No differences were detected for GYM versus NON in chronological age, nbFFM, arm length (not shown), Tanner breast stage, MAT or MEN (p>0.05, Table 1a). For the total sample, NON means were greater for height, weight, body mass index (BMI), PBF and waist circumference, whereas non-aquatic physical activity levels were greater in GYM (p<0.05). Within maturity levels, GYM exhibited consistently lower PBF, with higher physical activity levels. However, not all differences were consistent across maturity levels: only M3 GYM were significantly shorter; waist circumferences were smaller only in M1 and M2 GYM; and weight and BMI were significantly higher only in M2 NON. Among post-menarcheal subjects, GYM exhibited significantly higher age at menarche relative to NON, but gynecological age (years since menarche) was well-matched (Table 1a). Unadjusted values for bone outcomes are presented in Tables 1b and and1c1c.
GYM physical activity levels were 3-4 times higher than NON across maturity levels; for both GYM and NON, activity levels were higher in post-menarcheal than pre-menarcheal subjects. GYM had been participating in gymnastics for approximately 2 to 15 years (mean 6.5 yrs, sd 2.8), with starting ages ranging from 2 to 11 years (all premenarcheal: mean 5.5 yrs, sd 2.2). Although starting age did not differ significantly between maturity groups, it showed an increasing trend by MAT (M1= 4.8 yrs, sd 0.42; M2= 5.7 yrs, sd 0.31; M3= 6.1 yrs, sd 0.47; p< 0.08). GYMHRS was strongly positively correlated with years since training initiation (r= 0.62, p < 0.001), whereas there was no correlation between GYMHRS and age at training initiation (r= −0.08, p> 0.43).
GYM adjusted means were greater than NON for all outcomes at both 1/3 and UD RAD (GYM status main effect, p<0.05; Figures 1a,1b), indicating substantial osteogenic effects from gymnastic loading exposure during growth.
GYM adjusted means were greater than NON for FN BMC and FN aBMD (p<0.05) (Figure 1c). Similarly, significant differences were detected between GYM and NON for all NN HSA variables (Figure 1c), except NN CSMI and hip axis length (not depicted, raw data Table 1c). Differences included greater GYM NN cortical thickness (CT), NN bone tissue cross-sectional area (bCSA) and NN Z, accompanied by lower buckling ratio (NN BR, lower buckling ratio = greater cortical stability)(p<0.05). In contrast, GYM exhibited significantly lower NN width, endosteal diameter (ED) and shaft neck angle (last not depicted, raw data Table 1c). These findings suggest that gymnastic exposure during growth promotes FN strength via thickened cortices with narrower overall bone diameter, similar to jumping adaptations reported by Petit et al. .
Within GYM, GYMHRS exhibited positive, independent explanatory value for most RAD outcomes (5% to 15% of variance, p<0.05); exceptions included 1/3 aBMD, 1/3 ED, 1/3 CT and UD width (3% to 4% of variance, p≥0.09)(Table 2a). In these and all cases except CT, nbFFM was a potent, positive predictor of all RAD outcomes (19% to 74% of variance, p ≤0.001, Table 2a). When GYMHRS did not provide significant predictive value, height was substituted for nbFFM; this resulted in significant associations between GYMHRS and all RAD outcomes except ED, suggesting that a portion of the GYMHRS dose “effect” is via lean mass adaptation (Table 2b). In general, strong positive correlations with GYMHRS support the premise that gymnastic loading is the main stimulus driving GYM RAD advantages.
Within GYM, GYMHRS was negatively correlated with FN width, NN CSMI, NN ED, NN BR and shaft-neck angle (p<0.05), demonstrating a strong inverse trend with NN Z (p<0.06) (Table 2c). GYM HRS was positively correlated with FN and NNaBMD, as well as NN CT. With nbFFM in the model, GYMHRS did not exhibit significant explanatory value for FNBMC, NNbCSA, NNZ or hip axis length. When height was substituted for nbFFM, the predictive value of GYMHRS improved for FNBMC (+, p<0.05) and NNbCSA (+, p<0.09), but not for NN Z or hip axis length (Table 2d). These associations support the assertion that gymnastic loading is the main stimulus driving GYM FN advantages in CT, aBMD and BR, via restriction of FN periosteal and endosteal width.
At 1/3 RAD, significant GYM status × MAT interactions were detected for BMC (GYM advantages-M2: 13%, M3: 21%), Z (GYM advantages-M2: 20%, M3: 96%), width (M3 GYM advantage: 15%), ED (M3 GYM advantage: 18%) and cortical compartment cross-sectional area (cCSA, M3 GYM advantage: 40%), with greatest overlap for GYM advantages in M1 subjects and the clearest, highest magnitude GYM advantages in M3 (Figure 2c). Specifically, no advantages were detected for 1/3 ED in M1 or M2 comparisons, but M3 GYM exhibited nearly 20% larger ED than NON. For 1/3 width and cCSA, M1 GYM and NON did not differ; strong trends were exhibited for M2 GYM advantages (4% and 9%, respectively), and M3 GYM advantages were large and significant (15% and 40%, respectively). No GYM status × MAT interactions were detected for 1/3 aBMD or CT, indicating consistent GYM advantages across maturity levels.
At UD RAD, only BMC and index of structural strength in axial compression (IBS) demonstrated significant GYM status × MAT interactions (Figure 2b); GYM advantages were clear in all groups, increasing with maturity level (BMC: M1 24%, M2 35%, M3 55%; IBS: M1 44%, M2 62%, M3 96%; Figure 2b). In contrast, non-significant interactions indicated that GYM advantages in UD aBMD and width were consistent across maturity levels.
Although conclusions are limited by the cross-sectional nature of the data, ANCOVA results suggest that greater M3 GYM advantages are a function of lower RAD parameters for age and body size in M3 NON than all other groups. This pattern suggests that NON RAD bone accrual and expansion keep pace with total body growth until menarche, but are limited post-menarche. Thus, it appears that exaggerated M3 GYM RAD advantages are not due to an exaggerated post-menarcheal loading response (Figure 2b, 2c).
Within the GYM subset, only UD width demonstrated a significant menarche “effect” (Table 2a, ,2b).2b). Furthermore, no significant GYMHRS × MEN interactions were detected, except for 1/3 BMC and 1/3 aBMD; in both models, MEN and GYMHRS × MEN were excluded due to variance inflation > 17.0, as GYMHRS dominated. Substitution of MAT (M1-3) for MEN universally diminished explanatory value (results not presented).
All of the above suggest that physical maturation does not modulate loading “effects” or affect distal radius properties independent from age, nbFFM or loading within the GYM subset. However, as GYMHRS tended to be higher in post-menarcheal than pre-menarcheal GYM, intercorrelation of these variables may mask an underlying physical maturity effect. In fact, for many dependent variables (1/3 aBMD, 1/3 ED, 1/3 CT, UD width), PBF, age and/or MEN were significant RAD predictors, reducing the explanatory value of both nbFFM and GYMHRS. These relationships suggest that energy balance (1/3) and/or estrogen (UD) “effects” may mask dose-related loading “effects” for GYM bone geometric measures. Longitudinal analyses are necessary to evaluate within-subject change in bone parameters relative to body composition and physical maturity.
Significant GYM status × MAT interactions were detected only for FN BMC and NN BR (Figures 1c, ,2a).2a). For FN BMC, GYM advantages were greatest in M1 (11%), with overlapping confidence intervals for M3 differences (7%) and no M2 difference detected. For BR, M1 GYM had the clearest advantage, with 25% lower BR than comparable NON, whereas M2 GYM advantages were lower (-13%), and M3 confidence intervals overlapped (-11%). Findings for FN Area, BMC and aBMD were similar regardless of correction for fan beam magnification error; corrected results are presented.
In contrast to RAD results, FN results suggest that both GYM and NON experience peri-menarcheal gains in FN BMC that are exaggerated for age and body size. This potential estrogen “effect” appears to be more extreme in peri-menarcheal NON than GYM, resulting in lower GYM BR advantages for age and body size in M3 than M2 or M1 (Figure 2a). In all cases, cross-sectional analysis limits conclusions regarding maturity-specific differences; results must be confirmed via longitudinal evaluation of growth within-subjects.
For FN variables, no significant GYMHRS × MEN interactions were detected. When MAT was substituted for MEN, MAT exhibited inferior explanatory value (results not presented). In contrast to RAD, FN variables demonstrated a strong positive association with MEN in many nbFFM models, explaining 6% to 8% of variance for FNBMC, FNaBMD, NNbCSA and NNCT (p<0.05)(Table 2c). MEN explanatory value was even greater in height-based models of FNBMC, NNbCSA and NNZ (24-66%, p< 0.001), suggesting that strong intercorrelation between physical maturity and nbFFM may mask maturity effects. Interestingly, PBF was less influential as a predictor of FN than RAD outcomes, suggesting that physical maturity may be more influential than energy balance at this site. Again, longitudinal analyses are necessary for more conclusive interpretation of factors in intra-individual change through time.
As hypothesized, for all RAD outcomes, adjusted indices of bone geometry, areal density and strength were significantly greater in GYM than NON (Figure 1a, b). Also as hypothesized, for FN, GYM demonstrated significant advantages in adjusted indices of bone mass, areal density and strength compared to NON, but adjusted indices of FN periosteal and endosteal dimensions (NN width, NN ED) were significantly lower in GYM than NON. Furthermore, for comparable outcomes, effect sizes were larger for RAD than FN differences (% difference: RAD 6% to 66%, FN 4% to 17%).
As further corroboration of site-specific differences, for ratios of BMC/nbFFM, RAD advantages for GYM versus NON were clear and consistent across maturity groups (ANOVA p< 0.001, Figure 3, panels 1 & 2). In contrast, patterns for FN BMC/nbFFM ratios were inconsistent, such that mean ratios were greater in M1 GYM than NON (p = 0.002) but greater in M2 NON than GYM (p= 0.001), with no M3 difference detected (p= 0.36) (Figure 3, 3rd panel). Across maturity levels and activity groups, ratios were much higher for FN than RAD, reflecting the role of the femur as a habitual total body mass-bearing bone during most organized and daily life activities (Figure 3, panels 1-3).
Our results suggest a fundamental difference in geometric response to loading at FN versus RAD. To interpret this geometric distinction, one must consider the mathematics of the HSA formulae used to derive CSMI, Z and BR. CSMI is a function of bCSA and the sum of squared distances of each pixel of bone mass from the centroid (directly related to bone width and ED). Maximum bending strength, Z, equals CSMI/dmax(dmax= maximum distance from bending plane centroid). BR equals CT/dmax . For 1/3 RAD, bCSA and cCSA are considered interchangeable.
Assuming uniform bone tissue apparent densities, CSMI may be increased in 2 ways: 1) by increasing bCSA; 2) by distributing BMC more peripherally (via increasing width and/or ED). Because Z equals CSMI/dmax, Z may increase in 2 main ways: 1) by increasing CSMI (via increasing bCSA and/or distributing BMC more peripherally); or 2) by decreasing dmax (via decreasing bone width). At 1/3 RAD, it appears that M2 and M3 GYM Z are greater due to greater CT and cCSA, coupled with more peripheral BMC distribution post-menarche (M3 GYM width and ED advantages), thereby increasing CSMI (not calculated). In contrast, at FN, GYM do not exhibit a CSMI advantage. GYM NN Z is greater than NON due only to lower dmax (smaller bone width). Thus, as observed, GYM NN Z is greater than NON, despite no GYM NN CSMI advantage and smaller NN width. Finally, because BR equals dmax/CT, GYM buckling risk is lower than NON due to smaller NN width and greater NN CT.
All bone compartment results must be confirmed using 3D imaging techniques, as HSA and RAD DXA-derivations rely on assumptions of questionable validity (see limitations). Nonetheless, DXA plane FN Area and NN width both indicate more compact FN periosteal dimensions in GYM than NON, supporting the premise that patterns of bone geometric adaptation are site-specific.
Alternatively or in addition, the lower magnitude of GYM advantages at FN than RAD may indicate diminished GYM versus NON contrast for FN. This is a reasonable hypothesis, as many of our NON were likely to exhibit FN advantages associated with non-gymnastic loading modalities . Nikander and colleagues reported greater FN aBMD, NN CSA and NN Z in subjects who participated in “high and odd impact” activities compared to inactive controls, but no NN width differences were detected . Our NON were not inactive controls during the study period, and many were likely to exhibit benefits associated with participation in high impact (basketball, volleyball, track and field events, etc.) and odd impact (soccer, lacrosse, field hockey, dance/aerobics, etc.) activities during growth; thus larger GYM FN advantages would be expected in comparisons against sedentary controls.
The greater magnitude of observed GYM advantages at RAD than FN supports the preferential use of a distal radius model to highlight skeletal associations with gymnastic loading. Although the proximal femur is loaded by extremely high impact forces during gymnastics, as noted above, it is also loaded by other exercise, free play and daily life. Accordingly, the proximal femur loading pattern may not clearly distinguish gymnastics-specific adaptations from adaptation to background loading. Conversely, the non-dominant radius does not bear the total body mass during most activities, but as the primary load-bearing bone in the distal forearm during many gymnastic maneuvers, it sustains repeated total body mass impacts. Furthermore, impact dampening between the foot and the hip reduces force transmission to the proximal femur to a greater extent than forces are dampened at the distal radius; this concept is supported by particularly high magnitude UD GYM advantages compared to more proximal sites (UD BMC 37% versus 1/3 BMC 17% and NNBMC 5%; 66% UD IBS versus 1/3 Z 35%, NN Z 6% and NN BR 17%).
We compared our FN results directly to two studies that employed ANCOVA to adjust for height and weight, accounting for menarche status [25,26] (Table 3). No significant GYM status × MEN interactions were detected except for shaft-neck angle (current study). On the whole, all three studies suggested similar qualitative benefits attributable to gymnastic training. However, our study detected significant differences where the other studies did not, possibly due to greater sample size and statistical power (Table 3). For many variables, the magnitude of GYM advantages was greatest in the cohort examined by Maimoun and colleagues, as compared to advantages in the cohorts evaluated by the current study and Faulkner and colleagues. GYM in the study by Maimoun et al. trained at a higher intensity (19.9 h/wk) than our GYM (12.8 h/wk), supporting the premise that benefit magnitude may be a function of gymnastic exposure dose. In addition, a larger percentage of GYM in the Maimoun cohort were post-menarche (48%, versus 21% (current study) and 0% (Faulkner et al.)), likely indicating both greater accumulation of estrogen exposure and training duration in the Maimoun cohort.
Petit and colleagues published the results of a randomized controlled jumping intervention in pre-pubertal and early pubertal girls . Although no benefits were detected for pre-pubertal jumpers, pre-pubertal jumping exposure was associated with greater 7 month gains in NNaBMD, NNbCSA, NNZ and NNCT, with strong trends toward lower periosteal and endosteal expansion in jumpers than controls . In general, our FN results corroborate these findings. However, we did not detect significant loading × maturity interactions for most FN variables. In fact, our results suggest a contradictory (or opposite) loading × maturity interaction, as FNBMC and buckling ratio benefits were greater for age and body size in pre-pubertal (M1) than early pubertal girls (M2).
Unfortunately, inter-study comparisons of radius results are not straightforward, as studies vary in sample composition, methodologies and outcomes. Accordingly, there is no consensus on adaptation in periosteal and endosteal dimensions, which may vary by site, physical maturity and/or estrogen exposure [8, 20, 36-38]. Nonetheless, our results, and those of other studies, associate gymnastic exposure during growth with RAD advantages in theoretical strength and cortical dimensions in immature and mature females [8, 20, 36-38].
Two recent studies provide specific evidence to support the premise that greater RAD loading advantages after menarche are due to continued periosteal and endosteal expansion despite estrogen exposure, whereas conditions of lower relative loading allow estrogen exposure to limit periosteal and endosteal expansion for age and body size. Ducher et al. reported that female EX-GYM exhibited greater RAD periosteal and endosteal dimensions than NON, with greater advantages in amenorrheic than eumenorrheic EX-GYM (periosteal CSA: metaphysis 34% vs. 21%, diaphysis 38% vs. 32%; endosteal CSA: diaphysis 79% vs. 51%). These results support the premise that loading promotes expansion and estrogen opposes expansion.
Using a rat model, Leppanen and colleagues compared growth of the femoral diaphysis under conditions of: 1) control (+Loading (+L), +Estrogen (+E)); 2) ovariectomy (+L/-E); 3) hindlimb neurectomy (-L/+E); or 4) both interventions (-L/-E) . Compared to -L/-E, loading increased bending strength (asymmetrical periosteal and cortical expansion); addition of estrogen to loading subtly increased bending strength advantages by thickening cortices via lower endosteal expansion . In contrast, -L/+E yielded inconsistent bone strength advantages via greater cortical vBMD and endosteal contraction, without periosteal expansion. Thus, estrogen exposure may increase bone strength advantages attributed to loading via greater cortical thickening with slight limitation of periosteal and endosteal expansion. It is possible that such a loading × estrogen interaction plays a greater role at the femur than the radius, which would explain our limb-specific results.
As gymnastic training likely affects muscle and fat, adjustment for tbFFM and PBF may reduce the detected “skeletal loading effect”. Nonetheless, our analyses detected significant GYM advantages, whereas Faulkner and colleagues reported no GYM advantages after adjustment for tbFFM . Still, our main results may present a conservative view of skeletal adaptation to gymnastic loading compared to studies that do not adjust for body composition.
Although we did not detect significant interactions between gymnastic loading exposure and physical maturity for many variables, this does not mean that growth and adaptation processes are identical across maturity levels. Our cross-sectional analysis is not capable of detecting changes in bone parameters relative to loading exposure within individuals as they develop from one maturity phase to another. Similarly, reported maturity differences may be a function of greater cumulative and recent gymnastic loading doses with increasing maturity. Future longitudinal analyses will track intra-individual development, accounting for time-varying co-variates such as age, body size and menarche status and evaluating loading exposure as a continuous variable. Nonetheless, this preliminary cross-sectional analysis improves upon existing studies by using comparable methods to evaluate indices of bone geometry and strength at multiple sites within each individual.
Radius DXA-derived variables use simplified geometric models that assume equal cortical tissue volumetric BMD (vBMD) for GYM and NON. Our derivations attempt to account for cortical vBMD variability by applying Tanner stage-based cortical vBMDs to both activity groups [28,36]. Although a few studies have indicated lower cortical vBMD in ex-GYM versus NON [15, 37-38], it is unknown whether purported cortical vBMD differences are consistent across maturity levels. If cortical vBMD is systematically and uniformly lower in GYM than NON, GYM advantages in CT and cCSA would be underestimated by the current methods. Furthermore, because DXA-derivations appear to systematically underestimate RAD CT in larger bones , the current study may provide a conservative estimate of RAD CT advantages in GYM versus NON.
Similar assumptions limit HSA derivations. NN bCSA assumes uniform apparent bone tissue density of 1.05 g/cm3, relying upon: 1) similar apparent tissue density for both cortical and trabecular bone; 2) similar apparent tissue densities for GYM and NON; 3) similar apparent tissue densities across maturity groups. As discussed for RAD derivations, violation of these underlying assumptions may also influence FN HSA results. For derivation of NNCT, HSA assumes: 1) a circular NN model; 2) 60% of bCSA is cortical compartment and 40% is trabecular compartment. Just as for the radius, if there are loading-related differences in FN cortical tissue density, then our FN results represent conservative estimates of GYM advantages in NNCT, NNbCSA, NNBR and NNZ. Furthermore, relative proportions of the cortical versus trabecular compartments may differ in GYM versus NON (i.e. are not universally 60% cortical vs. 40% trabecular), yielding greater GYM advantages for NNCT and NNBR (thicker cortices and lower BR in GYM than NON).
Finally, the large number of bone outcomes evaluated increases the probability of Type I error. Significant main effects and interactions are expected based on chance alone in 5%, or 1.1/22 comparisons (excluding redundant variables reported only for context (Area, nnBMD)). As we expected differences to vary by site, it is more appropriate to evaluate significance levels by site: 1/3 α= 0.05/7= 0.007; UD α= 0.05/4= 0.0125; FN α= 0.05/11=0.005. Using these more stringent α levels and adjusting for age, height, nbFFM, PBF and MAT, all of our results remained similar except the following (no longer significant): 1/3 ED (main effect and interaction), FNBMC (main effect and interaction), NNZ (main effect) and shaft neck angle (main effect). For multiple regression analyses, any GYMHRS effects not noted as significant beyond the level of α=0.01 should be corroborated. Overall, even using more stringent alpha criteria to account for multiple testing, most of our findings are supported and corroborate those of other studies.
We evaluated both the distal radius and the proximal femur in a large sample of girls over a wide range of physical maturity and activity levels. Analogous methodologies were used to compare site-specific geometric adaptation within individuals. We identified site-specific differences in geometric adaptation patterns, such that GYM skeletal advantages were more consistent and of greater magnitude for distal radius than proximal femur outcomes. Specifically, loading at the distal radius diaphysis was associated with greater theoretical skeletal strength through larger periosteal and endosteal dimensions in post-menarcheal GYM than NON. In contrast, at the proximal femur, buckling ratio was more favorable due to greater gymnast bone tissue CSA and cortical thickness, despite narrower bone width and endosteal diameter. Although our analyses are cross-sectional, the results suggest: 1) accumulation of skeletal benefits with long-term loading exposure, 2) loading benefits that increase with estrogen exposure or 3) a combination of the two. Finally, we identified maturity-specific loading advantages at these sites; however, maturational processes must be elucidated in subject-specific longitudinal analyses.
Young, female gymnasts vs. non-gymnasts: Radius & femoral neck DXA-derived indices.
Two-factor ANCOVA tested for gymnastic exposure & maturity: effects, interactions.
Gymnastics: Greater geometry & strength benefits at radius than femoral neck.
Gymnastics: Larger cortices at both sites, wider radii vs. narrower femoral necks.
Gymnasts gain skeletal strength via maturity-& site-specific geometric adaptation.
We are grateful for the assistance of Portia Flowers and Rebecca Hickman in data management. We would also like to acknowledge the assistance of Jill Kanaley, Sue Hemingway, Rebecca Hickman, Tina Craig, Cathy Riley, Eileen Burd, Carol Sames and Kristy Kmack during data collection. Last but not least, we are very grateful for the cooperation and assistance of our study participants and their families. The project described was funded by grants from the Orthopedic Research and Education Foundation, SUNY Upstate Medical University, the National Institute of Arthritis, Musculoskeletal and Skin Diseases (R03AR047613; R01AR054145). This publication was made possible by grant number R01AR054145 from the National Institute of Arthritis, Musculoskeletal and Skin Diseases.
All authors have no conflicts of interest.
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