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Logo of nihpaAbout Author manuscriptsSubmit a manuscriptNIH Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
Osteoarthritis Cartilage. Author manuscript; available in PMC Oct 23, 2007.
Published in final edited form as:
Osteoarthritis Cartilage. Jul 2007; 15(7): 789–797.
Published online Feb 16, 2007. doi:  10.1016/j.joca.2007.01.011
PMCID: PMC2040334




Evaluation and treatment of patients with early stages of osteoarthritis is dependent upon an accurate assessment of the cartilage lesions. However, standard cartilage dedicated MR techniques are inconclusive in quantifying early degenerative changes. The objective of this study was to determine the ability of MR T and T2 mapping to detect cartilage matrix degeneration between normal and early OA patients.


Sixteen healthy volunteers (mean age 41.3) without clinical or radiological evidence of OA and 10 patients (mean age 55.9) with OA were scanned using a 3 Tesla (3T) MR scanner. Cartilage volume and thickness, T and T2 values were compared between normal and OA patients. The relationship between T and T2 values, and Kellgren Lawrence (KL) scores based on plain radiographs and cartilage lesion grading based on MR images were studied.


The average T and T2 values were significantly increased in OA patients compared with controls (52.04 ± 2.97 ms versus 45.53 ± 3.28 ms with P = 0.0002 for T, and 39.63 ±2.69 versus 34.74 ± 2.48 with P = 0.001 for T2). Increased T and T2 values were correlated with increased severity in radiographic and MR grading of OA. T has a larger range and higher effect size than T2, 3.7 versus 3.0.


Our results suggest that both in vivo T and T2 relaxation times increase with the degree of cartilage degeneration. T relaxation time may be a more sensitive indicator for early cartilage degeneration than T2. The ability to detect early cartilage degeneration prior to morphologic changes may allow us to critically monitor the course of OA and injury progression, and to evaluate the success of treatment to patients with early stages of OA.

Keywords: Osteoarthritis, Cartilage Imaging, Magnetic Resonance Imaging, T, T2


Osteoarthritis is a heterogeneous and multifactorial disease characterized primarily by the progressive loss of hyaline articular cartilage 1. Plain radiographs have been used primarily in the evaluation of OA, which depict only narrowing of the joint space or gross osseous changes that tend to occur late in the disease. Early changes in the articular cartilage may not be visible on plain radiographs. Cartilage loss can only be indirectly inferred by the development of joint-space narrowing, which can be highly unreliable even with careful attention to proper technique 2. In addition, plain radiographs are insensitive to focal cartilage loss, and widening of the joint space despite significant cartilage loss can occur in one compartment of the knee simply as a result of narrowing in the other compartment 3.

MRI has been found useful to visualize cartilage directly yet morphologic imaging shows damage at a stage when cartilage is already irreversibly lost. Standard cartilage dedicated MR techniques include fat saturated T2-weighted, proton density-weighted fast spin echo (FSE) sequences and T1-weighted spoiled gradient echo (SPGR) sequences. These sequences, however, are inconclusive in quantifying early degenerative changes of the cartilage matrix, especially biochemical changes such as proteoglycan loss 4. Early events in the development of cartilage matrix breakdown include the loss of proteoglycans, changes in water content, and molecular level changes in collagen 5. Early diagnosis of cartilage injury would require the ability to non-invasively detect changes in proteoglycan concentration and collagen integrity before gross morphologic changes occur.

T2 relaxation reflects the ability of free water proton molecules to move and to exchange energy inside the cartilaginous matrix. Damage to collagen-PG matrix and increase of water content in degenerating cartilage may increase T2 relaxation times. In vivo T2 relaxation times have been derived by several groups 610. Elevated T2 values were observed in patients with OA 7,10. T (T1rho) relaxation time has recently been proposed as an attractive alternative parameter to probe biochemical changes in cartilage 1115. The T parameter describes the spin-lattice relaxation in the rotating frame 16. It probes the slow motion interactions between motion-restricted water molecules and their local macromolecular environment. The extracellular matrix in articular cartilage provides a motion-restricted environment to water molecules. Changes to the extracellular matrix, such as proteoglycan loss, therefore may be reflected in measurements of T. Initial studies in human subjects showed elevated T values in patients with OA 1719. Although both T and T2 can probe slow motion of water protons, they are parameters describing different MR relaxation mechanisms. T is spin-lattice relaxation related with the energy changes between proton spins and the environment, while T2 is spin-spin relaxation related with the energy changes between proton spins themselves. Therefore, these two parameters may provide complementary information regarding macromolecular changes in cartilage.

With the improvement in cartilage resurfacing procedures and development of disease modifying drugs for OA, there is a need to develop a non-invasive method to monitor early cartilage degeneration or restoration 2023. In this study, we investigated the changes in T and T2 relaxation times in normal and osteoarthritic patients using 3T MRI. Our hypothesis was that there would be an increase in both T and T2 values in cartilage in osteoarthritic patients compared to normal controls. We further hypothesized that the amount of T and T2 elevation would be related to the severity of OA.



Sixteen healthy volunteers (eight female and eight male, ranging in age from 22 to 74 years, with an average age of 41.3 years) and 10 patients with clinical OA symptoms and radiological findings (three female and seven male, ranging in age from 37 to 72 years, with an average age of 55.9 years) were studied. Among them 10 healthy volunteers (four female and six male, ranging in age from 28 to 74 years, with an average age of 41.0 years) were scanned for both T and T2 mapping, while in the remaining 6 volunteers only T mapping was obtained. In all patients standard radiographs were obtained in addition to both T and T2 MR examinations. The study was approved by the Committee for Human Research at our institution and all of the subjects gave informed consent.

Imaging Protocol

In the patients, the standard knee radiographic protocol included 1) bilateral standing flexion weight-bearing view, 2) 30 degrees flexion lateral, and 3) bilateral patellofemoral, sunrise views.

All MR exams were implemented on a 3T GE Excite Signa MR scanner using a quadrature transmit/receive knee coil. The protocol included six sequences: sagittal T1-weighted spin-echo (SE) imaging (TR/TE = 700/13.5 ms, FOV = 16 cm, matrix = 288 × 224, bandwidth = 15.63 KHz, Number of excitations [NEX] = 2), sagittal and axial 3D water excitation high-resolution spoiled gradient-echo (SPGR) imaging (TR/TE = 15/6.7 ms, flip angle = 12, FOV = 16 cm, matrix = 512 × 512, slice thickness = 1 mm, bandwidth = 31.25 kHz, NEX = 0.75), sagittal fat-saturated T2-weighted fast spin-echo (FSE) images (TR/TE = 3700/68 ms, FOV = 14 cm, matrix = 288 × 224, slice thickness = 3 mm, echo train length [ETL] = 8, bandwidth = 16.5 kHz, NEX = 2), and axial T-weighted and T2-weighted images.

The multi-slice T-weighted images were obtained using the sequence we previously developed based on spin-lock techniques and spiral image acquisition 19. The acquisition parameters were: 14 interleaves/slice, 4,096 points/interleaf, FOV = 16 cm, effective in-plane spatial resolution = 0.6 × 0.6 mm, slice thickness = 3 mm, skip = 1 mm, number of slices = 14–16, TR/TE = 2000/5.8 ms, time of spin-lock (TSL) = 20/40/60/80 ms, spin lock frequency = 500 Hz. The total acquisition time was approximately 13 minutes. The axial T-weighted images were prescribed on sagittal SPGR images, covering regions from the top of the patellar cartilage to the femoral-tibial cartilage. The T2 quantification sequence was also based on spiral sequence 24,25 with TR/TE = 2000/6.7, 12, 28, 60 ms, All other prescription parameters of the T2 sequence were the same as the T sequence, with a total acquisition time approximately 11 minutes. The T2 quantification was acquired subsequently and covered the same region as the T sequence.

Plain Radiographic and Clinical Diagnostic MR Images Assessment

All radiographs and clinical MR images (SPGR, T1- and T2-weighted fat saturated sequences) were reviewed by a radiologist (T.M.L). The radiographic findings were scored according to the Kellgren-Lawrence (KL) scale, which is a standard grading system for OA 26,27. Osteophytes at the joint margins, narrowing of joint spaces and subchondral sclerosis have been considered as radiological features of OA. Based on these features, the following KL scores were defined 28: 0, no features of OA; 1, doubtful OA, with minute osteophytes of doubtful importance; 2, minimal OA, with definite osteophytes but unimpaired joint space; 3, moderate OA, with osteophytes and moderate diminution of joint space; and 4, severe OA, with greatly impaired joint space and sclerosis of subchondral bone.

The MR images were analyzed regarding cartilage lesions, joint effusion, popliteal cysts, ligaments and menisci. Additional features included reactive bone marrow changes, osteophytes, subchondral cysts and loose bodies. Five compartments were defined in each subject: patella, medial femoral condyle (MFC), lateral femoral condyle (LFC), medial tibia (MT) and lateral tibia (LT). Cartilage thinning was defined in each of the compartments based on T2-weighted FSE and T1-weighted SPGR images as: 0, no obvious thinning; 1, <50% thinning; 2, >50% thinning; and 3, full thickness loss of cartilage. Each patient was given an overall grade based on the most severe cartilage lesion in each of the five compartments. The bone marrow edema pattern was defined as high signal intensity in the T2-weighted fat-saturated FSE images and graded as: 0, no obvious BME; 1, mild edema with less than 1 cm diameter in the long axis; 2, moderate edema with diameter between 1 and 3 cm in the long axis; 3, severe edema with diameter larger than 3 cm in the long axis. Osteophytes were classified as: 0, no obvious osteophytes; 1, mild when they were located in the joint margins and were less than 0.5 cm in diameter; 2, severe when osteophytes were larger than 0.5 cm in diameter.

MR Images Post-processing

MR images were transferred to a Sun workstation (Sun Microsystems, Palo Alto, CA) for off-line quantification of cartilage volume and thickness, and quantification of T and T2 relaxation times.

Cartilage was segmented semi-automatically in sagittal SPGR images using an in-house developed program with MATLAB based on edge detection and Bezier splines 29. Five compartments were defined as mentioned above in each subject: patella, MFC, LFC, MT and LT. An iterative minimization process was used to calculate total cartilage volume and average thickness for each region. Following segmentation, a medial line was generated in each region of cartilage. The cartilage thickness was determined by calculating the minimum distance from each point on the medial line to a cartilage boundary. The average thickness was calculated for each slice and then averaged for all the slices. The cartilage volume was determined by multiplying the total number of voxels encompassing the cartilage by the volume of each voxel. The root mean square CV for intra-observer reproducibility of this algorithm was between 2.4%–3.69% as reported previously 30. Finally to minimize volumetric variations due to the size of the knee, the cartilage volume was normalized by the epicondylar distance determined from axial SPGR images.

The T map was reconstructed by fitting the image intensity pixel-by-pixel to the equation below using a Levenberg-Marquardt mono-exponential fitting algorithm developed in-house:


T-weighted images with the shortest TSL (therefore with highest SNR) were rigidly registered to high-resolution T1-weighted SPGR images acquired in the same exam using the VTK CISG Registration Toolkit 31. The transformation matrix was applied to the reconstructed T map. Different regions of the knee cartilage: patellar, trochlea, medial and lateral compartments were segmented automatically based on axial high-resolution SPGR images using the same algorithm used for sagittal segmentation. The segmentation was corrected manually to avoid synovial fluid or other surrounding tissue. 3D cartilage contours were generated and overlaid on the registered T map. Similarly, The T2 map was reconstructed by fitting the image intensity pixel-by-pixel to the equation S(TE)[proportional, variant] exp(−TE/T2). T2-weighted images with the shortest TE were rigidly registered to SPGR images, and the transformation matrix was applied to T2 maps using the VTK CISG Registration Toolkit. The cartilage contours generated previously from SPGR images were also overlaid on the registered T2 map. To reduce artifacts caused by partial volume effects with synovial fluid, regions with relaxation time greater than 150 ms in T or T2 maps were manually removed from the data used for quantification.

Statistical Analysis

A non-parametric rank test was used to compare volume, average thickness, average T and T2 values between control subjects and OA patients. A Spearman rank correlation was performed to study the relationship between average T and T2 values, between these relaxation times and ages, and between these relaxation times and cartilage thickness and volumes. The effect size was calculated to compare the discrimination power of T and T2 values using equation below:


where Δ mean is the mean difference between control and OA, and SD is the pooled standard deviation of these two groups defined as:


Where n1 and n2 are the sample size of these two groups respectively, and SD1 and SD2 are the standard deviation of these two groups respectively.


T and T2 Quantification for Control Subjects and OA Patients

The average T values were significantly higher in OA subjects compared with healthy controls (52.04 ± 2.97 ms versus 45.53 ± 3.28 ms, P = 0.0002), as shown in Table 1. The average T2 values were also increased significantly in patients with OA (39.63 ± 2.69 ms versus 34.74 ± 2.48 ms, P = 0.001, Table 1). Figure 1 shows T and T2 maps for a healthy control. Figure 2 and Figure 3 present T and T2 maps of a patient with mild OA with KL score = 1, and a patient with advanced OA with KL score = 4, respectively. The average T and T2 values correlated significantly (R2 = 86.0%, P < 0.0001). T values had a higher effect size than T2 values (3.7 versus 3.0), indicating T may be more sensitive than T2 for distinguishing OA from controls.

Figure 1Figure 1Figure 1
T1-weighted water excitation SPGR image (a), T map (b) and T2 map (c) for a healthy control (male, 30). No radiographs were obtained, as the subject is a healthy asymptomatic control. No cartilage thinning, osteophytes and other OA symptoms ...
Figure 2Figure 2Figure 2Figure 2
Radiographs (a), T1-weighted water excitation SPGR image (b), T map (c) and T2 map (d) for a patient with mild OA (male, 66). From radiographs, no significant joint space narrowing was seen, but minimal osteophytes were observed in femoro-tibial ...
Figure 3Figure 3Figure 3Figure 3
Radiographs (a), T1-weighted water excitation SPGR image (b), T map (c) and T2 map (d) for a patient with advanced OA (male, 46). Based on radiographs, the patient had joint space narrowing with 1 mm in medial compartment and 3 mm in lateral ...
Table 1
Radiological findings based on radiographs and anatomic MR images

The average T values increased with age in the 16 healthy controls, with a significant but moderate correlation (R2 = 58.3%, P = 0.018), as shown in Figure 4. In the ten controls who also had T2 quantification, T2 values also increased with ages, but the correlation was not significant (R2 = 41.5%, P = 0.233).

Figure 4
Distribution of T values versus age in healthy volunteers. The correlation is moderate but significant with R2=58.3% and P=0.018.

KL Scores and MR Findings Based on Anatomic MR Images

Based on radiographs, two patients had a KL score = 1, three had a KL score = 2, three had a KL score = 3 and two had a KL score = 4. Cartilage lesions were classified as grade 0 for one patient, 1 for three patients, 2 for two patients and 3 for four patients. Table 2 illustrates the main findings based on radiographs and clinical MR images for the 10 patients, including KL score, cartilage lesion grade in each compartment, osteophytes in the femoro-tibial joint, femoro-patellar joint and the joint center, as well as bone marrow edema. Among the ten OA patients, six patients had more severe cartilage lesions at the medial compartments than at the lateral compartments, two had more severe lesions at the lateral compartments, and two had the same lesion grade at both compartments.

Table 2(a)
Cartilage thickness (in mm, mean ± SD) in each compartment

There were no significant difference in the total volume and average thickness of cartilage in OA patients and control subjects (1.53 ± 0.42 cm3/cm versus 1.27 ± 0.29 cm3/cm for volume normalized by epicondyle length, and 1.78 ± 0.31 mm versus 1.65 ± 0.32 mm for thickness), (P = 0.13 and P = 0.37 respectively). Table 3 presents the mean and SD of cartilage volumes and thickness in each compartments for control subjects and OA patients. There were no significant differences in either cartilage volume or thickness for any compartment between these two groups.

Table 3
T and T2 values (in ms, mean ± SD) in healthy controls and osteoarthritic subjects.

Relationship between Radiological Findings and T and T2 Quantification

The average T value increased as KL score increased based on radiographs, with 45.5 ± 3.3 ms, 47.6 ± 3.0 ms, 51.8 ± 0.7 ms, 52.4 ± 0.2 ms and 55.6 ± 0.4 ms for KL = 0 (healthy controls), 1, 2, 3, 4 respectively, Table 4(a). The same trend was found between average T2 values and KL scores, with T2 values of 34.7 ± 2.5 ms for grade 0, 35.9 ± 1.4 ms for grade 1, 39.8 ± 2.4 ms for grade 2, 39.6 ± 0.3 ms for grade 3 and 43.0 ± 1.0 ms for grade 4, as shown in Table 4(a).

Table 4(a)
T and T2 values (in ms, mean ± SD) in subjects versus KL scores evaluated on plain radiographs

The average T and T2 values increased as the overall cartilage lesion grades increased from 0 to 3 based (from 46.1 ± 3.6 to 54.4 ± 1.5 ms for T, and from 35.0 ± 2.5 ms to 41.4 ± 2.0 ms for T2 as presented in Table 4(b). No significant correlation was found between T and T2 values and cartilage volumes and thickness (P > 0.05).

Table 4(b)
T and T2 values (in ms, mean ± SD) in subjects versus cartilage thinning grades evaluated on MR images

Based on the cartilage lesion grading, we regrouped the 50 compartments for the 10 OA patients into two groups: mild OA with grades 0 and 1, and advanced OA with grades 2 and 3. The average T values were significantly increased in compartments with advanced OA compared with the ones with mild OA (54.3 ± 6.1 ms versus 48.4 ± 5.6 ms, P = 0.0012). The increase in percentage was 12.2%. The T2 values were also elevated in the compartments with advanced OA (41.0 ± 4.5 ms versus 38.0 ± 4.8 ms, P = 0.030), but with an increased percentage of only 7.9%.


In this study, we have demonstrated that both T and T2 cartilage values were significantly increased in patients with OA when compared with healthy controls. T and T2 values also increased with more severe radiographic OA and MR grades of cartilage degeneration.

Increased T2 values were reported previously in degenerated cartilage in both animal models and in human subjects 7,10,32. The values obtained in our study are consistent with the reported values, with a range from 31.3 ms to 38.7 ms for healthy controls and 35.0 ms to 43.8 ms for patients with OA. In an effort to correlate the T2 relaxation times with biochemical changes in cartilage, previous in vitro studies have reported that T2 correlated poorly with PG content 33,34, and PG cleavage did not affect T2 values significantly 35. Instead, T2 can be affected mainly by collagen content and orientation and/or water content 11,36. It has been observed that loss of proteoglycan is an initiating event in early OA, while neither the content nor the type of collagen is altered in early OA 5. Therefore lack of specificity to quantify proteoglycan loss may make T2 less appealing for early detection of cartilage degeneration. In addition, the angular dependency of T2 values with respect to the external magnetic field B0 have made it difficult to define a ‘normal’ appearance of T2 maps. As a result, it is difficult to apply T2 values to quantify cartilage degeneration longitudinally, and the clinical results obtained with T2 quantification remain inconclusive. This angular dependency, however, as shown in an in vitro study using high field (8.6T) microscopic MRI (μMRI), can provide specific information about the collagen ultra-structure 37.

T has been recently proposed as an attractive alternative to evaluate biochemical changes in cartilage matrix non-invasively. T relaxation rate (1/T) has been shown to decrease linearly with decreasing PG content in ex vivo bovine patellae 11 and has been proposed as a more specific indicator of PG content than T2 relaxation in trypsinized cartilage 33 and in human cartilage specimens obtained from patients with severe OA who underwent total knee replacement 38. Makela et al. 14 and Duvvuri et al. 39 have suggested that proton exchange between chemically shifted NH and OH groups of proteoglycan and the tissue water could be an important relaxation mechanism contributing to T relaxation. Therefore T may be specific to changes of proteoglycan in cartilage matrix during early stages of OA. Furthermore, T relaxation times do not seem to be affected by the orientation of collagen that can affect T2 relaxation techniques 40. Preliminary in vivo studies have also shown increased cartilage T values for patients with OA versus healthy controls 1719 Our results also suggested that the mean T values exhibit similar changes with age as seen in previous studies on T2 relaxation times 7,41.

The results of our comparison study demonstrated that both T and T2 techniques can be sensitive to cartilage degeneration. However, there is a larger range and effect size for T versus T2 values, which may indicate a more sensitive method of detecting cartilage degeneration. Furthermore, although there is a significant correlation between the average T and T2 values, the spatial distribution of the elevation of these two parameters can be different in OA patients, as clearly seen in Figure 3. We will investigate in the spatial correlation between T and T2 values in future studies. We believe that since T and T2 represent two relaxation mechanisms in tissues, they may provide complementary information on cartilage degeneration. Combining this information may enhance our ability to detect early cartilage degeneration, as well as to distinguish between different stages of degeneration.

In this study, T and T2 increased with KL scores based on radiographs and overall cartilage lesion grade based on analysis of clinical MR sequences. However, due to the small sample size, we could not test the statistical significance of this correlation. In a previous study correlating in vivo T2 values and OA disease severity as defined by KL scores, Dunn et al. 10 showed that the T2 values were elevated significantly in mild OA (KL=1,2, n=20) compared with healthy controls. Although there was an increasing trend of T2 values from mild OA to severe OA (KL=3,4, n=28), this difference was not significant. The authors proposed that with the limitations by KL grading system, in particular the emphasis on the presence of osteophytes, significant changes in T2 values for cartilage with different KL scores are not necessarily expected. Interestingly in this study, significant differences were observed in both T and T2 values between mild OA compartments (with cartilage thinning grade 0 and 1) and advanced OA compartments (with cartilage thinning grade 2 and 3) after we regrouped all 50 compartments according to cartilage lesion grade.

Furthermore, among the patients with cartilage thinning observed in MR images (grade >= 1), six had ‘spared’ compartments with cartilage thinning grade 0 on the clinical MR images. The average T and T2 values for these ‘spared’ compartments were 50.8 ± 5.4 ms and 39.4 ± 3.8 ms respectively. These values were significantly higher than those found in cartilage of healthy controls (P = 0.029 and P = 0.004 for T and T2 respectively). These results suggest that cartilage degeneration, or the biochemical change, can take place in these compartments even if no morphologic changes are yet visualized.

In this study, we did not find a significant difference in cartilage volume or thickness between the healthy control and OA groups. We attribute the lack of volumetric differences to the fact that early osteoarthritic patients with less structural cartilage wear were examined and to the varying severity of OA in the diseased group. The cartilage volume and thickness was slightly higher in the osteoarthritic subjects. This may due to the increase of water content and consequently swelling of cartilage in the early stages of OA. One example of segmented cartilage in medial compartments in a control (male, 30) versus an OA patient (male, 66) is shown in Figure 5. Our findings also indicate that physical measures such as cartilage thickness and volume may lag behind biochemical and molecular changes which can be measured quantitatively with T and T2 values.

Figure 5Figure 5
Segmented femoral and tibial cartilage in medial compartments of a healthy control (a, male, 30) and an OA patient (b, male, 66). The average thickness (in mm) is 1.68 vs. 1.84 (control vs. OA) in medial femoral condyle (MFC), and 1.63 vs. 1.71 (control ...

T and T2 imaging are a few techniques that have shown the potential of MR imaging to reflect changes in the biochemical composition of cartilage with early OA. Other techniques, including sodium 23 (23Na) MRI 42,43 and delayed gadolinium enhanced MRI of cartilage (dGEMRIC) 4446 have also shown promising results in imaging cartilage biochemistry. All of these techniques are complementary to standardized cartilage sensitive images and may provide information about cartilage changes (either proteoglycan or collagen) that may exist prior to structural changes in cartilage thickness or surface morphology. However, some of the techniques may have requirements that can limit their clinical use. The dGEMRIC technique, which has been validated in multiple studies to allow assessment of the proteoglycan component of articular cartilage, requires a several hour wait after either an intraveneous or intraarticular injection of the contrast agent (Gd-DPTA) for effective penetration. 23Na MR imaging, which uses sodium concentrations as a marker for proteoglycan loss, is of limited clinical use because of the inherent low sensitivity of sodium signal and the limited availability of sodium MRI (requires special coils and hardware).

T and T2 mapping does not require the use of special hardware, coils or contrast. Our study was implemented on a 3T MR scanner because of the advantages afforded by using a higher field strength (such as increased signal to noise ratio and higher resolution), but T-weighted MR images can be easily obtained on more readily available 1.5 T scanners 47.

A potential limitation of this study was that average T and T2 values were quantified within the entire cartilage surface or in a specific compartment of the knee. Mosher et al. has developed techniques examining the spatial variation of T2 within cartilage and reported changes in different layers with age and with cartilage degeneration 48. It may be helpful to further investigate the spatial variation of T in different layers and compare it with that of T2 values in both healthy controls and osteoarthritic subjects to better localize areas of cartilage degeneration.

In conclusion, in vivo T and T2 mapping techniques have demonstrated feasibility in detecting cartilage degeneration. Quantitative cartilage imaging may enhance our ability to detect subtle, early matrix changes associated with cartilage injuries when used in conjunction with standardized cartilage sensitive imaging. We are currently investigating the ability of quantitative imaging to detect cartilage injuries associated with ligament tears 49. Development of non-invasive methods to assess early cartilage matrix changes is potentially important to initiate early treatment, monitor disease progression and to follow-up operative cartilage repair and resurfacing.

Table 2(b)
Cartilage volume (normalized by epicondylar length, in cm^3/cm, mean ± SD) in each compartment


The authors would like to thank Dr. Robert Stahl for his help with radiograph data. The research was supported by NIH RO1 AG17762, RO1 AR46905 and K25 AR053633.


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