High-Resolution Peripheral Quantitative Computed Tomography for the Assessment of Bone Strength and Structure: A Review by the Canadian Bone Strength Working Group

Abstract

Bone structure is an integral determinant of bone strength. The availability of high resolution peripheral quantitative computed tomography (HR-pQCT) has made it possible to measure three-dimensional bone microarchitecture and volumetric bone mineral density in vivo, with accuracy previously unachievable and with relatively low-dose radiation. Recent studies using this novel imaging tool have increased our understanding of age-related changes and sex differences in bone microarchitecture, as well as the effect of different pharmacological therapies. One advantage of this novel tool is the use of finite element analysis modelling to non-invasively estimate bone strength and predict fractures using reconstructed three-dimensional images. In this paper, we describe the strengths and limitations of HR-pQCT and review the clinical studies using this tool.

Introduction

High-resolution peripheral quantitative computed tomography (HR-pQCT), commercially available in the mid-2000’s, is a non-invasive, low-radiation method for assessing bone microarchitecture and volumetric bone mineral density (BMD) in cortical and trabecular compartments of the distal radius and distal tibia. Its application in clinical research has increased exponentially in the past decade (Fig. 1), and has enlightened our understanding of age-related changes and sex differences in bone microarchitecture, differences in bone structure across a wide range of bone metabolic disorders, fracture risk, and the response of bone to different osteoporosis therapies. Coupled with computer-based finite element analysis (FEA) modeling, HR-pQCT also provides a newfound approach to noninvasively assess bone strength.

Fig. 1.

The number of publications each year that utilized high-resolution peripheral quantitative computed tomography

Currently, only one commercial HR-pQCT machine, the XtremeCT (SCANCO Medical AG, Brüttisellen, Switzerland), is able to perform scans at a resolution sufficient to measure three-dimensional human bone microarchitecture in vivo. However, research groups worldwide are working collaboratively to advance HR-pQCT post-image processing algorithms to better quantify the observed changes.

The Canadian Bone Strength Working Group is an interdisciplinary academic group established in 2007 that has interests in advancing bone strength research and education. Although HR-pQCT is currently a research tool, there is potential for its use in the clinical diagnosis and management of osteoporosis. Our group recently performed a systematic search of published literature in the adolescent and adult population up until January 31, 2013 (Medline search terms “high-resolution peripheral quantitative computed tomography” OR “HR-pQCT”, no limitations). In this paper, we aim to provide a comprehensive review of the methodology, limitations, and clinical utility of HR-pQCT with an emphasis on its use to study aging and gender differences, fracture discrimination, and treatment effects.

HR-pQCT Scanning Techniques

Image Acquisition

Patient Positioning

As with any medical imaging device, the proper positioning of the patient is crucial to accuracy and reproducibility. The most common usage of HR-pQCT is to image the non-dominant radius and tibia in vivo. The scanner’s gantry is relatively narrow and shallow (rear physical stop) only allowing the distal peripheral skeleton to be accommodated. Although rare, some individuals with large lower leg girth are not able to fit within the scanner bore.

The limb being scanned is immobilized in a carbon fiber shell (Fig. 2a). A scout view, essentially a two-dimensional x-ray scan, is obtained so that the operator can identify a precise region for the three-dimensional measurement (Fig. 2b, c, d). The standard measurement protocol utilizes the following settings: an X-ray tube potential of 60 kVp, X-ray tube current of 95 mA, matrix size of 1536 × 1536 and slice thickness and in-plane voxel size of 82 μm. While the reconstructed voxel size is 82 μm for the standard patient HR-pQCT protocol, the actual spatial resolution of the image is approximately 130 μm near the center of the field of view, and somewhat less off-center (140–160 μm) [1, 2•]. Consequently, structures less than 100 μm are not typically resolved from in vivo images. At each site, 110 computerized tomography slices are obtained and used to reproduce a 9.02 mm (radial or tibial length) three-dimensional image (Fig. 2e).

Fig. 2.

a, A typical setup of HR-pQCT for patient measurements. At top, the casts used for securing the forearm and lower leg is shown. b, c, and d, The procedure for HR-pQCT analysis requires a ‘scout view’ x-ray of the radius or tibia (left) so that the operator can select the region of interest for scanning (solid green bar). Subsequently, three-dimensional data can be obtained in the scan region (right). e, A typical section from HR-pQCT showing the ultradistal tibia and fibula. The green line on the periosteal surface of the tibia is used to extract the bone of interest for subsequent three-dimensional analysis

Because HR-pQCT uses a polychromatic X-ray source it is subject to beam hardening as well as scatter artefacts, which can significantly impact geometric and densitometric measures [3]. Daily and weekly quality control scans should be performed to identify drift, which can occur as a consequence of decreased X-ray emission (decay). The HR-pQCT single-scan effective dose is estimated to be 3 μSv [4]. Given that exposure is additive, we recommend no more than three measures at a single site during an appointment due to the recommended radiation dose limit being 50 μSv/year (International Commission on Radiological Protection).

Motion Artefact

Because HR-pQCT has a high resolution and scan times are relatively long (3 minutes), any movement during the scan can result in movement artefact, impacting the accuracy and reproducibility of the images obtained or rendering the image unusable. Measures of micro-architecture are more sensitive to movement artefact compared with geometric or densitometric measures [5–7, 8•]. While automated and well-defined manual grading techniques to quantify and correct for motion artefact have been developed [7, 8•, 9, 10], the best solution to date is to re-scan the patient as the effect of motion on parameter errors are typically not systematic and correction algorithms cannot be applied to the parameters themselves [9].

Automated motion detection does provide the possibility for real-time assessment of scan quality allowing for the operator to decide whether a re-scan is necessary [8•]. Pialat et al [6] reported that in 22.7 % of their scans motion artefacts necessitated a re-scan. Looking forward, improved immobilization would improve data quality and minimize the need for re-scanning.

Image Registration

When a patient needs to be followed longitudinally, image registration is applied to ensure the same region is consecutively assessed. The HR-pQCT system includes a default image registration that matches repeat scans by aligning similar-sized slices. More sophisticated three-dimensional registration methods have also been developed [4, 11].

Image Analyses

Once the images have been acquired, a default patient evaluation protocol is used to analyze the scans over the entire 9.02 mm three-dimensional region to assess a wide range of standard and optional structural and density parameters, defined in Table 1 (Fig. 2d presents a typical HR-pQCT section).

Table 1.

HR-pQCT parameters with units

	Abbreviation	Description	Standard unit
Metric measures
Total volume	TV	Volume of entire region of interest	mm3
Bone volume	BV	Volume of region segmented as bone	mm3
Bone surface	BS	Surface area of the region segmented as bone	mm2
Bone volume ratio*	BV/TV	Ratio of bone volume to total volume in region of interest	%
Bone surface ratio	BS/BV	Ratio of bone surface area to bone volume	%
Trabecular thickness*	Tb.Th	Mean thickness of trabeculae	mm
Trabecular thickness SD	Tb.Th.SD	Measure of homogeneity of trabecular thickness	mm
Trabecular separation*	Tb.Sp	Mean space between trabeculae	mm
Trabecular separation SD	Tb.Sp.SD	Measure of homogeneity of trabecular spacing	mm
Trabecular number*	Tb.N	Mean number of trabeculae per unit length	per mm
Cortical thickness (original)*	Ct.Th	Average cortical thickness	mm
Cortical porosity	Ct.Po	Cortical porosity	%
Bone mineral density (D100)*	BMD	Total volumetric density	mg HA/cm3
Cortical bone mineral density (Dcomp)*	Ct.BMD	Cortical volumetric density	mg HA/cm3
Trabecular bone mineral density (Dtrab)*	Tb.BMD	Trabecular volumetric density	mg HA/cm3
Total bone area*	Tt.Ar	Cross-sectional area	mm2
Non-Metric Measures
Structural model Index	SMI	Measure of trabecular structure (0 for plates and 3 for rods
Degree of anisotropy	DA	1 is isotropic, >1 is anisotropic by definition; DA = length of longest divided by shortest mean intercept length vector
Connectivity density	Conn.D	Extent of trabecular connectivity normalized by TV	mm-3
Cross-sectional moment of inertia	l min, 1 max	minimum and maximum moments of inertia	mm4

*Standard HR-pQCT measures are indicated

Standard Measures

A good description of the techniques used to provide three-dimensional measures are given in Boutroy et al 2005 [12], and it is important to recognize that although these analysis methods are based on techniques developed for micro-computed tomography (μCT), some of the parameters with HR-pQCT are derived rather than directly measured (eg, trabecular thickness), because the voxel size of the scanner is close to the average thickness of a human trabecular structure [13, 14]. In future versions of HR-pQCT scanners, it may be possible to directly measure all microarchitecture parameters; however, that is not currently possible with the standard analysis protocol.

Secondary Analyses

The three-dimensional data from HR-pQCT offers opportunities to develop new techniques and parameters to describe and quantify the plate and rod-like structure of bone. These include structure model index [15], connectivity density (initially developed for μCT of ex vivo bone) [16, 17], and individual trabecular segmentation (ITS) [18]. Methods have also been established to improve the segmentation of the cortical and trabecular compartment [19, 20, 21•], and subsequently measure cortical parameters such as cortical porosity [21•, 22•]. There are other applications under development, such as for the visualization and quantification of bony erosions in a rheumatoid arthritis hand [23]. Certainly, these and future analyses will continue to add value to HR-pQCT measurements.

Accuracy and Precision

The HR-pQCT systems have been thoroughly tested for both accuracy and precision using μCT of ex vivo bone as the gold-standard. Whereas accuracy is typically assessed using cadaver data, precision is based on repeated measures analyses from in vivo scanning.

Accuracy

There is moderate to good agreement (r² = 0.59–0.98) between the HR-pQCT and μCT for the assessment of cadaveric morphological parameters [1, 24–28]. Other assessments, such as connectivity density (r² = 0.90) [24], mechanical stiffness (r² = 0.73) [24] and cortical porosity (r² = 0.80) [28] correlate highly with μCT [28]. Liu et al [29] tested ITS against μCT and found that measurements of HR-pQCT images correlated significantly with those of μCT images at a similar voxel size (80 μm, r = 0.71–0.94) and correlations were stronger for plate-related parameters compared with trabecular rods. Tjong et al [1] investigated the impact of different voxel sizes (41, 82, and 123 μm) on HR-pQCT accuracy and found that the 41 μm voxel size correlated best with the μCT measures and the 123 μm voxel size worst for trabecular microstructure and cortical porosity measures. Trabecular density and cortical thickness measures were strongly correlated with μCT across all voxel sizes.

When compared with the gold-standard μCT, HR-pQCT provides moderate to good accuracy in assessing bone structural indices in the radius and tibia.

Reproducibility

Essential to any clinical measurement is the demonstration that measures are reproducible. BMD assessment by HR-pQCT is highly reproducible, with precision errors generally below 1 % [4, 5, 12, 22•]. Structural measures, not surprisingly, have higher precision errors associated with them, ranging from 2.5 %–6.3 % [4, 5, 12, 22•]. FEA intrinsically incorporates a composite of BMD and structural data and has a precision error between that of its components (<3.5 %) [4].

HR-pQCT measures performed at the radius consistently have worse precision than those at the tibia [5, 22•] and in vivo measures have a higher precision error than those ex vivo (ex vivo 0.5 %–1.5 %) [4], both likely owing to greater movement artefacts in the radius (a site easily affected even by the slightest movement of the head, neck, shoulder, arm, or fine tremors of the hand).

Initial work to characterize multi-center precision has begun through a consortium of HR-pQCT centers using anthropomorphic phantoms incorporating cadaveric radii [2•]. Using these phantoms, the ex vivo multi-center precision error across nine HR-pQCT systems was found to be <3 % for density measures and 4 %–5 % for trabecular structure measures. These data will be the basis for testing and validating cross-calibration techniques in the future. Improved automation of all aspects of data acquisition, analysis, and quality assurance will also be integral to multi-center standardization.

Segmentation

When analyzing bone, there are generally two bone compartments considered: cortical and trabecular. At the transitional zone, the confluence of these two compartments, there is little in the way of clear defining borders, presenting a significant challenge [30]. The standard analysis protocol involves the user manually defining the periosteal surface of the tibia or radius on each slice and a semi-automated contouring algorithm enables this manual process to be typically completed within five minutes. Subsequently, the analysis continues with a filtering and threshold approach that segments the cortical and trabecular bone compartments so that individual compartment analyses can be made. Typically this segmentation process has difficulties in properly identifying the cortex in cases where it is thin or highly porous.

A dual-threshold approach was introduced to address the challenge of bone compartment segmentation. This approach employs a series of fully-automated image processing steps and has proven to be in excellent agreement with hand-contouring of μCT images of the same bones (r = 0.9 to 1.0) [19]. This dual-threshold approach was further improved in a collaboration between the manufacturer and researchers in Calgary and San Francisco and is now available as part of the software package for all users of HR-pQCT [22•].

Alternative segmentation approaches have recently been proposed, including a threshold-independent segmentation tool that was shown to have a high degree of agreement with hand-contouring [20]. Most recently, another method that bases segmentation (and cortical porosity measurements) on a density profile analysis across the cortex [21•], may also allow for the identification of the transitional zone [30] between the cortical and trabecular compartments. Currently, both of these methods are implemented on third party platforms and therefore require data conversion and transfer procedures.

Heterogeneity in Bone Structure in Population Studies

Changes with Age

An important development for HR-pQCT adoption is the establishment of normative databases that provide age- and sex-specific reference data to allow comparison of individual subject data to population-level variation. Normative databases help with the clinical interpretation of HR-pQCT data by allowing for the production of reports that provide context to an individual’s HR-pQCT results. It also provides information about the changes in bone microarchitecture as a function of sex and age (albeit from cross-sectional studies of populations). To date there have been three main population-based HR-pQCT studies that have described age-related variation in bone microarchitecture – the Calgary cohort of the Canadian Multicentre Osteoporosis Study (CaMOS) cohort, the Rochester, Minnesota cohort and the Cambridge, UK cohort [31••, 32, 33]. Table 2 details the changes in HR-pQCT parameters over age.

Table 2.

Heterogeneity in bone structure in population studies — changes over age and between sexes (all cross-sectional studies)

Author year [reference]	Ages (y)	f/m	Volumetric bone density changes	Cortical compartment structural changes	Trabecular compartment structural changes
Liu 2010 [77]	9–21	172/151	BMD & Ct.BMD ↑ over puberty in f & m	Large ↑ in Ct.Th over puberty in f & m	Tb.Th ↑ in f & m over puberty; little change in Tb.N
Nishiyama 2012 [34]	9–22	212/186	More mature ↑ Ct.BMD	More mature ↓ Ct.Po	m ↑ BV/TV & ↑ Ct.Ar vs f
Boutroy, 2005 [12]	19–88	256	PM f ↓ BMD, Ct.BMD & Tb.BMD vs pre-menopausal f	PM f ↓ Ct.Th vs pre-menopausal f	PM ↓ Tb.Nb & Tb.Th vs pre-menopausal f
Nishiyama 2010 [28]	19–99	280/0	PM f ↓ Ct.BMD vs pre-menopausal f	PM f ↑ Ct.Po; Ct.Th was similar in PMf and pre-menopausal f	N/R
Burghardt 2010 [38•]	20–78	94/57	BMD & Ct.BMD & in f & m;	m ↑ Ct.Th vs f; Co.Po increased with age in m & f, but more so in f	N/R
			PM f ↓ To.BMD & Ct.BMD vs pre-menopausal
Dalzell 2009 [32]	20–79	74/58	Tb.BMD ↓ f vs m; BMD, Tb.BMD & Ct.BMD all ↓ with age	Ct.Th ↓ in f vs m and loss faster over age in f	m ↑ Tb.N & Tb.Th vs f; no relationship between age and change in trabecular structure
MacDonald, 2011 [31••]	20–99	442/202	BMD & Ct.BMD ↓ in f & m; decreased faster in f	Tt.Ar ↑ through adulthood; ~33 % ↑ young m vs young f	m ↑ Tb.N & Tb.Th vs f; over aging both ↓ Tb.Nb & Tb.Th
Khosla 2006 [33]	21–97	324/278	Ct.BMD ↑ young f than m, but decreased faster in f with aging (22 vs 16 %)	Ct.Th ↓ faster in f with aging vs m (52 vs 38 %, p = 0.001)	young m ↑ Tb.BV (26 %) & Tb.Th (28 %) vs f; Tb.Nb ↓ with age in f but not in m; Tb.Th ↓ more in men with age vs f
Bjornerem 2011 [37]	40–61	185/0	N/R	PM f ↑ Ct.Po & ↓Ct.Ar vs premenopausal f	PM f ↓ Tb.N & BV/TV vs premenopausal f

BMD Total BMD, BV/TV trabecular bone volume/total volume, Ct.Ar cortical bone area, Ct.BMD Cortical BMD, Ct.Th Cortical thickness, Ct.Po cortical porosity, f female, m male, N/R Not reported, PM postmenopausal, Tb.BMD trabecular BMD, Tb.Nb trabecular number, Tb.Th trabecular thickness, Tt.Ar total bone area

During puberty, there is a general increase in cortical BMD and a decrease in cortical porosity with a corresponding increase in estimates of bone strength in both sexes [34, 35]. It has also been suggested that transient increases in cortical porosity coincide with the age of highest fracture incidence, during early puberty [36]. With the exception of early puberty, young men have a higher estimated load-to-strength ratio (estimated failure load divided by fall force), or in other words, lower estimated fracture risk.

After puberty, total bone area tends to increase with age, with men generally possessing a larger cross-sectional area compared with women (~33 % larger) [31••]. Postmenopausal women have larger intracortical and endocortical bone surface area compared with premenopausal women [37]. Cortical thickness is higher in men than in women, but declines in both sexes with age and over the menopause [12, 32]. Cortical porosity is higher in young men, but increases with age and after menopause in women [28, 31••, 38•]. In dual energy x-ray absorptiometry (DXA)-assessed areal bone mineral density (aBMD)-matched populations of young (<50 years) and elderly (>50 years) women and men cortical porosity measures alone showed age-related increases (approximately +90 % and +30 % for women and men, respectively) [39].

Young men tend to have similar or greater numbers of trabeculae that are thicker compared with young women [31••, 32, 33]. This results in a greater trabecular bone volume/tissue volume (BV/TV) in young men compared with young women (20–29 years) [33]. Changes after young adulthood have been described as loss of trabecular number and thickness in both genders with aging [31••], decreases in trabecular number only in women with aging and relatively larger losses in trabecular thickness in men [33] and no change in either parameter with age [32]. Postmenopausal women have lower trabecular number compared with premenopausal women [12, 37].

As measured by FEA, young men have stronger bones than young women (34 % to 47 % greater) but both sexes have losses in strength with aging [31••, 32]. The percentage of load carried by trabecular bone increases with aging in both sexes [32] and increases in cortical porosity have shown through FEA to be important determinants of strength [38•]. Load-to-strength ratios tend to increase more in women than in men with aging (27 % more) [31••].

Differences in Relation to aBMD

Osteopenic and osteoporotic women (defined by aBMD) generally have weaker bone in almost all parameters assessed by HR-pQCT when compared with women with normal aBMD [18, 28]. Areal (DXA-estimated) BMD is higher in men than in women, and declines with age [32] and through menopause [12]. However, not all studies have found an age-associated decline in volumetric BMD by HR-pQCT [38•].

Individuals with similar DXA-based aBMD can have vast differences in results determined by HR-pQCT. Substantial variation in indices reflecting density, structure, and biomechanical competence exist among subjects with identical aBMD results [40]. This could be attributable to differences in bone structure, measurement site, artifacts, or measurement methodology.

Role of HR-pQCT for Fracture Risk Assessment

HR-pQCT has been demonstrated to be able to discern between women and men with and without fractures. The inherent strength of HR-pQCT is its ability to assess a large slice of bone in three-dimensions for differences in cortical and trabecular characteristics and to identify those characteristics that are most associated with bone weakness, by FEA bone strength modelling.

When compared with DXA aBMD, HR-pQCT measures have a better discriminatory ability to discern between women with and without fractures [16, 41•, 42–44, 45•, 46–48, 49••], even those with similar aBMD [50, 51•]. Differences in HR-pQCT assessed cortical thickness and porosity, BMD, and decay in trabeculae explain a lot of the discriminatory ability. While HR-pQCT bone quality measures are particularly sensitive to discriminate forearm fractures from controls [16, 41•], vertebral fractures appear to be more strongly associated with poor bone quality compared with non-vertebral fractures in general [52–54]. Many of these measures are independent of those assessed by DXA [43, 44].

Ex-vivo examinations comparing DXA and HR-pQCT have concluded that aBMD was highly correlated with BMD and a number of HR-pQCT-obtained microstructural parameters [55]. When combining a DXA-calculated polar moment of inertia measure with aBMD the prediction of specimen structural failure was similar to that obtained by the HR-pQCT measures.

Overall, there is emerging evidence that HR-pQCT is generally superior to DXA for discriminating men and women with and without fractures, especially at the sites of measure (ie, distal radius), although all studies to date were cross-sectional.

Finite Element Analysis Modeling

Many fractures occur in individuals with normal or osteopenic aBMD, and not only in individuals with aBMD in the osteoporotic range. While density is a reasonable surrogate for bone strength, the assessment of bone mechanical properties by FEA may improve identification of those at high risk for fracture because it provides a more comprehensive measure of bone strength based on both bone microarchitecture and BMD of each tiny element from the three-dimensional image. FEA parameters at the radius and tibia are associated with all types of fragility fractures in both men [56•] and women [57].

FEA modeling has also been shown to accurately predict the energy needed for fracture in ex vivo studies. At the wrist, FEA models have correlated highly with bone stiffness (r² = 0.79) and strength (r² = 0.87–0.96) obtained with mechanical testing [58–60]. In many of these models, the zones that display high strains are those where fracture subsequently occurred [58].

Emerging FEA approaches include the use of accelerated computational performance based on either multiple central processing unit cores, or even multiple graphics processing unit cores. It is now possible with some software applications to analyze a typical HR-pQCT scan on standard consumer workstations in under two minutes, compared with hours on less-optimized systems [61].

Role of HR-pQCT in Monitoring Therapy

There are current limitations to the use of DXA in monitoring osteoporosis therapies. The percent of fracture risk reduction attributable to changes in aBMD with different therapies varies from 5 % to 85 % [62–66]. HR-pQCT presents the potential to monitor other components of bone strength, with possibly greater discrimination between different osteoporosis therapies. Thus, the interest in applying HR-pQCT to clinical research studies has grown significantly in recent years, and data from recent studies have provided interesting insights into the effect of new and existing osteoporosis therapies on bone structure and strength.

Treatment with alendronate over one and two years largely preserves BMD, cortical thickness, trabecular BV/TV, and estimated failure load [67, 68, 69••]. One study found that after two years of alendronate therapy there were significant improvements in BMD, cortical thickness and cortical area at the distal tibia, but not at the radius [70]. Treatment with zoledronic acid for 18 months significantly increased total BMD, cortical BMD, cortical thickness, and trabecular BV/TV at both sites, but had no impact on cortical porosity [71]. FEA revealed maintenance of bone strength with zoledronic acid therapy. After two years of ibandronate therapy, there was no change in trabecular bone microarchitecture, however at the tibia there was a preservation of cortical thickness and gains in cortical BMD [72]. One year of treatment with denosumab resulted in maintenance or increases in total, cortical, and trabecular BMD and cortical thickness [69••].

One year of strontium ranelate therapy increased trabecular BMD, cortical thickness, and cortical area [68]. Two years of treatment with strontium ranelate resulted in increases in cortical BMD, cortical thickness, trabecular BV/TV, and FEA-estimated failure load [67]. These data may be affected by beam hardening from the artifact of the higher atomic number of strontium compared with calcium incorporated in bone.

Odanacatib therapy has been shown to increase total, cortical, and trabecular BMD as well as increase cortical thickness at both the radius and the tibia after two years of therapy [73]. FEA demonstrated an increase in the estimated failure load (increased bone strength) at both sites with odanacatib therapy over two years.

Teriparatide therapy for 18 months results in decreases in total BMD, cortical BMD, and cortical thickness with concomitant increases in cortical porosity [71, 74]. Teriparatide therapy was also associated with trabecular thinning, an increase in trabecular number and reduced trabecular BV/TV at the wrist [71]. Despite these changes in bone quality, bone strength was maintained over the 18-month follow-up [71, 74]. With PTH 1-84 there is a loss of estimated bone strength at the radius and tibia strength after 18 months of therapy [71].

Limitations and Challenges of HR-pQCT

It is important to recognize that HR-pQCT only assesses bone at two sites of the peripheral skeleton typically, and there is a concern whether measurements at these sites reflect strength at the axial skeleton (ie, hip and spine). There is limited data, but the few studies that have examined the relationship between HR-pQCT measurements of the peripheral skeleton have shown a moderate correlation (r = 0.56–0.70) to the axial skeleton [75, 76]. Furthermore, it is important to emphasize that the radius itself is an important fracture site, and certainly there is no better imaging technology available than HR-pQCT to measure bone structure at that site. The value of the tibial measurement in relation to fracture is less directly relevant, but the value of having a tibial measurement is that it is a weight-bearing site, as opposed to the radius. Lastly, evidence is still emerging as to whether the distal radius (or tibia) is a responsive skeletal site for monitoring therapy; however, evidence based on the clinical trials conducted to date are encouraging (as noted above).

Segmentation is a continuing challenge, and a focus of much energy in technology development. Despite the fact that HR-pQCT is the highest resolution in vivo scanner available for human bone measurements, the 82 μm voxel size poses challenges in segmentation because a human trabeculae is close in physical dimension. In addition, direct quantification of porosity is limited to relatively large Haversian canals that are resolvable by HR-pQCT. Furthermore, identifying the delineation between the cortical and trabecular compartments is challenging, largely because a precise border is not always present due to real biological effects in the endocortical and intracortical envelopes. Various strategies have been developed, as discussed earlier, but the most crucial aspect is the reproducibility rather than the accuracy of the segmentation process. Removing operator bias has the advantage of producing more reproducible data, as well as ensuring consistency among HR-pQCT centers. Nevertheless, this is an area of HR-pQCT methodology that requires more work.

There are several other technical issues, such as the partial volume effect, beam hardening, and assumptions in the calculations of all the structural and densitometric measures. While not all of these errors can be corrected, it is important to recognize that they exist and interpret the findings accordingly. For example, measures such as the structural model index, which is highly sensitive to image resolution, should be interpreted with caution when derived from HR-pQCT, because it is highly sensitive to motion artifacts, which can occur especially when scanning the radius. Density-based measures may be susceptible to beam hardening and scatter artifacts.

Conclusions

HR-pQCT provides unprecedented ability to measure human bone microarchitecture at the wrist and ankle in the clinical setting, and these data are providing new insight into changes in bone quality across the lifespan as well as the impact of anti-osteoporosis therapies on bone quality. Before this cutting edge research tool can be used in routine clinical practice, it is imperative to show its utility for fracture prediction, either in conjunction with DXA-based aBMD or in lieu of DXA. While today HR-pQCT is strictly a research tool, it is a relatively easy technology to utilize in the ‘standard analysis’ or automatic analysis default mode, thus opening the possibility for wider use in the hands of ‘non experts’. If it can be demonstrated that HR-pQCT provides value to bone quality assessment, the currently prohibitive cost of the systems would likely be substantially decreased as production increases. Currently, there are less than 45 HR-pQCT systems world-wide, compared with thousands of DXA machines. With the development of normative databases, it will be possible to provide better context of the outcome measures from HR-pQCT, similar in concept to the T-scores that are routine outputs from DXA scan reports. Fracture risk assessment (such as FRAX) could potentially be adapted to include HR-pQCT parameters.

In summary, the three-dimensional measurement of bone by HR-pQCT confers significant advantages over two-dimensional measurements based on DXA. It provides assessment of not only BMD, but also of bone structure and strength. To fully realize the potential of this technology for clinical use, many more clinical studies in different populations will need to be performed.