Quantification of 99mTc-DPD concentration in the lumbar spine with SPECT/CT
© Cachovan et al.; licensee Springer. 2013
Received: 25 March 2013
Accepted: 24 May 2013
Published: 5 June 2013
Routine single-photon emission computed tomography (SPECT) currently lacks quantitative information on regional activity concentration (ACC) of the injected tracer (e.g. kBq/ml). Furthermore, little is known on the skeletal absolute concentration of 99mTc-DPD after intravenous injection in bone scintigraphy. The aim of this study is to determine ACC in the healthy lumbar vertebrae of patients using a recently published quantitative SPECT/computed tomography (CT) protocol.
Lumbar vertebrae ACC estimates were performed in 50 female patients (mean age 69.88 ± 13.73 years) who had been administered 562.84 ± 102.33 MBq of 99mTc-DPD and had undergone SPECT acquisition 4 h after the injection. The SPECT/CT system was calibrated against a well counter. Images were reconstructed with Flash3D. ACC and CT tissue density were measured in volumes of interest drawn over the spongious bone tissue of the three lower lumbar vertebral bodies when these exhibited no focal CT or SPECT pathology.
Average ACC measured in the normal spongious bone tissue was 48.15 ± 13.66 kBq/ml (95% confidence interval (CI) 45.81 to 50.50 kBq/ml). This corresponds to a mean standardised uptake value (SUV) of (5.91 ± 1.54) (95% CI (5.64 to 6.17) SUV). SUV correlated significantly with Hounsfield units (HU) (r = 0.678, p < 0.0001). Significant negative correlations were observed between age and HU (r = −0.650, p < 0.0001) and between age and SUV (r = −0.385, p < 0.0001).
The SUVs determined for 99mTc-DPD uptake 4 h post injection are in the same range as those reported for [18F]fluoride in positron emission tomography. The strong correlation of SUV with bone CT density underlines the physiological significance of this variable. Our data suggest further investigation of the potential value of ACC measurement in the diagnosis of pathological conditions such as osteoporosis or in following up osseous metastases under therapy.
KeywordsQuantitative SPECT SPECT/CT Bone scintigraphy
Quantitative single-photon emission computed tomography (QSPECT) was first introduced into nuclear medicine in the 1990s. Rosenthal et al. predicted in 1995 that estimates of absolute SPECT tracer concentration would enter the clinical arena in the near future . However, to date, their prediction has not come true as only few approaches to QSPECT have been established in clinical practice (for reviews, see Ritt et al.  and Bailey et al. ).
Gilland et al.  and Tsui et al. [5, 6] have shown that several physical phenomena have to be taken into account to achieve absolute quantification in SPECT. One of the first QSPECT protocols validated in humans was reported by Willowson et al.  who quantified the concentration of 99mTc in the cardiac cavity of patients studied by radionuclide ventriculography. Also our research group  proposed a QSPECT protocol to quantify the tissue concentration of 99mTc. Our methodology, as well as that by Willowson et al., involves the use of co-registered data from X-ray computed tomography (CT) to correct for attenuation and a window subtraction approach (dual energy window) to correct for scattered counts.
In a recent review paper, Bailey and Willowson  predict a strong research interest in quantitative SPECT in the near future and suggest quantitative bone 99mTc scanning to be one of the potential fields of clinical interest. However, little is known on the accumulation of bone-seeking SPECT radiopharmaceuticals in the skeleton in absolute terms. Before the advent of hybrid imaging combining SPECT with CT, Israel et al.  used an empirical method to quantify osseous concentration of 99mTc-methylene diphosphonate (MDP). Their approach did not include corrections for attenuation. Therefore, the standard deviations in their results of lumbar tracer concentration amounting 30% to 40% of the mean were inevitable, motivating further research in that field.
Building on the methodological set-up developed by Zeintl et al. , we measure in this study the activity concentration (ACC) of 99mTc-diphosphono-propanedicarboxylic acid (DPD) in the spongious bone tissue without focal SPECT and CT abnormalities in women referred for bone scintigraphy. Furthermore, we correlate tracer concentration with bone density and age. Due to the dependence of Hounsfield units (HU) on various factors including patient shape and size , we also compute and collect linear attenuation coefficients (LAC)  and investigate their correlation with ACC.
In order to obtain quantitative results, multiple calibrations were necessary. Calibrations were performed using a protocol proposed by Zeintl et al. . We adopt and cite the proposed methods in the following description.
In vivo patient data analysis was carried out with permission from the Ethical Committee of the University of Erlangen-Nuremberg. We acquired data for a group of 50 female patients (mean age 69.88 ± 13.73 years; minimum 25 years, maximum 97 years) undergoing 99mTc-DPD bone scintigraphy of the lumbar region between February and August 2012 using a standard SPECT/CT protocol as described in the study of Zeintl et al. . The injected activity of 99mTc ranged from 5.60 to 10.30 MBq/kg (mean 8.26 ± 1.41 MBq/kg) corresponding to 151 to 278 μCi/kg (mean 223 ± 38 μCi/kg). The mean total activity administered was equal to 562.84 ± 102.33 MBq (15.21 ± 2.77 mCi). SPECT/CT was performed 4 h after intravenous injection.
The patients in our group were included based on the following criteria:
Start of SPECT acquisition within an interval of 4 h ± 30 min post injection
Access to data on measured injection activity, time of measurement, time of injection, residual activity measurement and time of residual activity measurement
Access to patient's weight and height information
At least one vertebral body of the lumbar vertebrae (LV 3, 4 and 5) in the field of view (FOV) of both SPECT and CT acquisitions
Absence of any kind of metal or surgical implants in the LV FOV
Based on patient records, there are two main groups of patients: those studied for work up of back pain (22) and those examined for staging malignancy (28). In 22 cases of the latter, the primary malignancy had been diagnosed in the breast. One woman was diagnosed with both breast and ovarian cancer. There was one case involving each of the following carcinomas: ovarian, oesophageal, renal cell and Ewing's sarcoma and osteoid osteoma.
All three LVs in the 45 patients examined and only two LVs in the 5 patients examined were in the FOV. Overall, 145 LVs were considered in this study.
Data acquisition and reconstruction
We used both Symbia T6 and Symbia T2 (CT with a maximum of six and two slice acquisitions per rotation, respectively, Siemens Healthcare, Molecular Imaging, Hoffman Estates, IL, USA) system at the Nuclear Medicine Clinic in Erlangen, Germany to acquire in vivo patient data. SPECT scans were acquired using low-energy high-resolution collimation, a 128 × 128 matrix of 4.8-mm pixel size and a total of 120 projections over 360° with a dwell time of 15 s/view. Subsequent to the SPECT acquisition, a low-dose CT scan was acquired with 130 kV and 30 ref mAs using adaptive dose modulation (CARE Dose 4D available for both Symbia® T6 and T2; Siemens Healthcare ). The CT data were generated with a 2.5-mm slice thickness using a smooth reconstruction kernel (B08s, Siemens Healthcare ) and a 1-mm slice thickness using a medium kernel (B41s, Siemens Healthcare).
SPECT reconstruction was performed using Flash3D (Siemens Healthcare, Molecular Imaging) [13, 14]. Flash3D is an ordered subset expectation maximisation (OSEM) reconstruction algorithm with depth-dependant 3D (axial and trans-axial) resolution recovery, scatter correction using scatter window subtraction (dual energy window approach) and attenuation correction based on attenuation maps derived from the CT data filtered with the B08s kernel. The OSEM SPECT reconstruction used four subsets and eight iterations without post-smoothing, as suggested by Zeintl et al. .
From the 145 vertebral bodies (LV 3 to 5), all vertebrae exhibiting any focal SPECT or CT pathology in their spongious bone tissue were excluded from the analysis based on the diagnosis defined by an experienced physician. The rationale for this was the intention to measure ACC in spongious bone tissue not affected by malignancy, compression fractures, osteochondrosis or facet disease. Overall, 133 vertebrae were selected for analysis based on the criterion previously defined. Five LV 5, three LV 4 and four LV 3 were rejected.
We also computed, based on the work of Zeintl et al. , the ACC underestimation for the selected VOIs. This was accomplished using the emission recovery coefficient tables for our particular operation point (VOI size and acquisition parameters) as defined in the work of Zeintl et al. . These recovery coefficients were obtained using simulations of hot spheres of different diameters in hot bath and were validated using real phantom acquisitions.
In the ‘Results’ subsection, we report various quantitative measures, including bone density expressed in HU and tracer ACC expressed in kilobecquerel per millilitre (kBq/ml) and SUV. The data are described by their mean values, their standard deviations and their 95% confidence intervals (CI). The correlation of the variables is analysed using linear regression yielding Pearson's correlation coefficients. The statistical significance of differences in the correlation coefficients was tested using Fisher's transformation (z and p values). Significance was accepted at p < 0.05. Statistical analysis was performed using MedCalc for Windows, version 18.104.22.168 (MedCalc Software, Mariakerke, Belgium).
Results and discussion
Statistical analysis of all variables collected for 50 female patients and 133 vertebral bodies
65.98 to 73.78
65.59 to 73.19
159.00 to 162.44
Administered activity (MBq)
533.76 to 591.92
Activity per 1 kg BW (MBq/kg)
7.86 to 8.66
45.81 to 50.50
5.64 to 6.17
3.74 to 4.05
5.69 to 6.17
% ID per ml (10−3)
8.12 to 9.39
Bone density (HU)
96.57 to 116.46
0.167 to 0.170
Correlation analyses between the measures of tracer uptake and the CT-based bone density variables
HU correlation ( r)
Age correlation ( r)
LAC correlation ( r)
The results collected using the two different VOI selection methods correlated significantly (p < 0.0001). The coefficient of determination (R2) values for HU, ACC (kBq/ml) and SUV were 0.95, 0.94 and 0.91, respectively. The mean underestimation of activity in the selected VOIs was 23.6% ± 1.3%.
In contrast to positron emission tomography (PET), SPECT is, to date, not routinely used for quantifying ACC in absolute terms in the clinical context. This is due to the lack of protocols correcting for the factors confounding ACC measurement by SPECT such as tissue attenuation and scatter. However, with the advent of SPECT/CT offering CT-based attenuation correction for routine clinical use, the efforts to develop truly quantitative SPECT have considerably gained in momentum. For example, Zeintl et al.  studied quantitative recovery of SPECT for various sphere sizes and for increasing the iteration number. In their subsequent work, they quantified the ACC of 99mTc-DPD in SPECT/CT images of the bladder, compared it to ACC determined in urine samples measured in a well counter cross-calibrated against the SPECT system used and reported a mean quantitative accuracy of 1.1% ± 8.4% (95% CI, −15.4% to 17.5%) . Likewise, Willowson et al.  studied absolute ACC for cardiac applications in phantoms using corrections for attenuation and scatter and reported a mean difference of −1% (range, −7% to 4%) for the calculated tracer activities. In their clinical validation study , they compared tracer activities measured using SPECT in the cardiac cavity after the injection of 99mTc-labelled erythrocytes with ACC determined in blood samples and reported a mean error of about 1% (range, −6% to 5%). Such previous work shows that ACC measurements in absolute terms are feasible in a clinical setting with regular SPECT protocols.
Quantitative estimations go hand in hand with system calibration in the routine. PET systems are calibrated on a daily basis. For current SPECT routine homogeneity verifications, quality controls and peaking calibrations are performed. A regular calibration with a 99mTc-filled uniform phantom as proposed in the study of Zeintl et al.  would be beneficial for quantitative SPECT to ensure that system volume sensitivity is stable or needs adjustments in the computations. In our experience, the system behaviour is stable over time. The sensitivity can vary between SPECT systems from different vendors and for differently sized phantoms as Seret et al.  have shown. They report relatively small error bars (−3.83%, 4.15% and 0.76%) for a NEMA standard phantom with a SPECT/CT Symbia system similar to those used in this study.
Building on the protocol developed by Zeintl et al., we extend their work to determine ACC in spongious bone tissue in patients referred for skeletal scintigraphy, which is one of the most common nuclear medical procedures. We compared the VOI selection using thin layers in the middle of the vertebral body and with ellipsoids, which contained most of the spongious bone in the vertebral body. The high R2 value between the two approaches shows the validity of the thin-layer VOI selection approach.
Research aimed at quantifying the uptake of diphosphonates by the skeleton was conducted in the 1970s and 1980s. Various groups [20–22] used whole body planar examinations along with blood and urine sampling to quantify tracer uptake. One-day retention of 99mTc-DPD was reported by Buell et al. to be about 40% . The results from these publications also served as a basis for the radiation dose report published by Weber et al. that contains dose calculations for various bone imaging agents .
However, owing to the problems in quantifying ACC in humans described in this study, data on the regional ACC in, for example, spongious bone is still scarce. Israel et al. used an empirical thresholding approach to quantify the concentration of 99mTc-MDP 2 to 4 h after injection in vivo on SPECT data sets reconstructed with filtered back projection without attenuation or scatter correction and reported a mean concentration percentage of about 5 × 10−3 of injected activity per millilitre in the lumbar spine for normal patients . Israel et al. did not report the resulting ACC in kilobecquerel per millilitre. Based on the reported injected activity ranging from 740 to 925 MBq, the ACC would be in the range of 37 to 46.25 kBq/ml. We used 99mTc-DPD SPECT data which were reconstructed using OSEM with depth-dependent 3D resolution recovery as well as correction for attenuation and scatter. We also corrected the injected activity for the residual activity remaining in the syringe after the injection (8.11% ± 2.97%), minimising quantitative errors. In our data, mean tracer uptake as measured in CT- and SPECT-unremarkable spongious bone of the lumbar spine was 8.75 ± 2.23 × 10−3 % ID per ml and 48.15 ± 13.66 kBq/ml. The higher DPD concentration compared to MDP is consistent with the properties of these imaging agents reported by Buell et al. .
Zeintl et al. [8, 17] simulated the behaviour of SPECT in spherical lesions using phantoms and defined correction tables for partial volume (PV). In our study, we computed the underestimation of the activity based on their PV correction methodology and obtained a mean tracer activity underestimation of 23.6% ± 1.3%. The correction tables were defined for spherical lesions having a lesion-to-background contrast ratio of 1 to 12 in the work of Zeintl et al. . In order to compute an AC underestimation factor, a value interpolation between the known VOI sizes is necessary. This is not possible for VOIs of non-spherical shape which behave differently. We anticipate that the quantitative error in the vertebral body is smaller due to cross talk from the adjacent osseous tissue not only in the axial but also in the dorsal direction. To prove this assumption, a phantom simulation study needs to be conducted which is out of the scope of this paper. Partial volume correction methods based on phantoms and simulations will clearly give accurate results for phantoms and a good approximation for similarly shaped regions with homogeneous activity distribution in patients, such as for the bladder as shown in the study of Zeintl et al. . In order to correct for partial volume effects in more complex structures and lesions, simulation studies adapted to their shape and size will have to be performed, ideally tailored to each individual patient. However, this is not feasible on a routine clinical basis. Different VOI selection, e.g. data maximum, or thresholding techniques even lead to a more complex behaviour which can exaggerate noise and create overshoots common in OSEM as well as Gibbs artefacts in the reconstructed volume .
In PET, ACC measurement is part of the clinical routine. Frost et al.  determined ACC 1 h after intravenous injection of [18F]fluoride to be 5.5 SUV. With our results, we give more insight to SPECT bone ACC, identify tracer uptake in female patients 4 h post injection and report a mean tracer uptake of 5.91 SUV for 99mTc-DPD in spongious osseous tissue that is of the same magnitude as for [18F]fluoride uptake in PET 1 h post injection. Clearly, PET is superior to SPECT in terms of spatial resolution when today's imaging technology is considered. Nevertheless, SPECT bears the potential of technological improvement; furthermore, SPECT has the advantage of lower costs and, at least at present, better availability than PET in most countries .
The diphosphonates bind to the calcium-rich tissue and the mineral phase of bone hydroxyapatite [27, 28]. Bone density correlates with hydroxyapatite's physical and structural density in the bones as well as with HU determined using CT . Our results show, the thus expected, strong correlation of tracer activity concentration with bone density expressed in HU (r = 0.678).
Bone density decreases with age, in particular in women [30, 31]. The significant correlation between bone density in HU and patient age is thus not unexpected. Bone density as well as age correlated significantly with normalised ACC expressed as SUV (r = 0.678 and r = −0.385) as well as with ACC (kBq/ml) (r = 0.483 and r = −0.379, respectively). The significantly stronger correlation of SUV and HU (z = 2.41, p < 0.05) compared to ACC (kBq/ml) and HU can be attributed to the reduction of the dependence of the correlations tested on administered dose as a confounding variable in this analysis.
CT measurement of HU is patient-dependent and its precision varies strongly with patient size and the body part examined. By incorporating a calibration phantom in the scanned FOV, quantitative CT (QCT) can correct for these factors . In our study, we simulated QCT using attenuation maps generated during SPECT reconstruction. The results showed highly significant correlations between LAC and SUV (r = 0.586, p < 0.0001) and suggest further investigation of this type of approach for bone density measurement.
Our data paved the road towards the usage of ACC and SUV in clinical routine for diagnostic purposes. One interesting indication in this context would be to use these variables to monitor therapy of bone metastases. More specifically, they could be used as adjunct to the RECIST criteria which to date have neglected the behaviour of bone metastases on CT and magnetic resonance images for methodological reasons .
The significant correlation between ACC and SUV on the one hand and HU and age on the other suggests the use of quantitative SPECT to study osteoporosis or other diseases involving bone metabolism. Nevertheless, QCT would be expected to be more precise for quantification of bone loss. QCT, however, does not allow the assessment of dynamic indices of bone metabolism such as bone turnover. Cook and co-workers studied quantitative [18F]fluoride PET in a dynamic acquisition setting  and could, therefore, also calculate kinetic parameters of skeletal fluoride uptake. Zeintl et al.  have shown that quantitative dynamic SPECT is feasible with current-generation, commercially available equipment. SPECT/CT thus harbours the potential for the precise assessment of diseases affecting bone turnover such as osteoporosis.
Osseous ACC of 99mTc-DPD reflects bone metabolism only indirectly as this variable is also influenced by tracer delivery to the osseous tissue. To allow for the calculation of the transfer constants describing bone metabolism, a measurement of the time radioactivity concentration curves in the arterial blood is necessary, which was not performed in this study. Furthermore, the binding of the polyphosphonate used by plasma proteins would have to be taken into account. The latter point is also important in view of the differences in plasma protein binding reported for the different bone-seeking 99mTc-labelled agents . All of these factors may be influenced by various diseases, e.g. renal insufficiency or hyperparathyroidism so that their analysis is important also in the clinical context.
A limitation of this paper is that we investigated DPD in adult women only. Therefore, the data proffered can only cautiously be generalised to men or younger subjects. All patients in whom SPECT/CT had been performed had indeterminate lesions in the lumbar region on planar scans which in most cases corresponded to degenerative disease of the spine as to be expected in the age group studied. The VOIs for measuring ACC and bone density were, however, only placed in spongious bone tissue not exhibiting focal SPECT or CT abnormalities. Therefore, the values reported herein are not affected by degenerative or malignant diseases.
The SUV values determined by SPECT/CT for DPD uptake of CT- and SPECT-normal spongious bone are in the same range as those reported for [18F]fluoride measured using PET. The strong correlation of SUV with bone CT density underlines the physiological significance of this variable. Our data suggest the further investigation of the potential value of ACC measurement in the diagnosis of pathological conditions such as osteoporosis or in the follow-up of osseous metastases under treatment.
The authors would like to thank Philipp Ritt, Bernard Bendriem, PhD, Ron Malmin, PhD, Manojeet Bhattacharya, PhD and Amos Yahil, PhD for valuable discussions and the technologist staff at the Nuclear Medicine Clinic at Friedrich-Alexander University Erlangen-Nürnberg for performing the SPECT/CT acquisitions.
- Rosenthal MS, Cullom J, Hawkins W, Moore SC, Tsui BMW, Yester M: Quantitative SPECT imaging: a review and recommendations by the Focus Committee of the Society of Nuclear Medicine Computer and Instrumentation Council. J Nucl Med 1995, 36: 1489–1513.PubMedGoogle Scholar
- Ritt P, Vija AH, Hornegger J, Kuwert T: Absolute quantification in SPECT. Eur J Nucl Med Mol Imaging 2011, 38: 69–77. 10.1007/s00259-011-1770-8View ArticleGoogle Scholar
- Bailey DL, Willowson KP: An evidence-based review of quantitative SPECT imaging and potential clinical applications. J Nucl Med 2013, 54: 83–89. 10.2967/jnumed.112.111476View ArticlePubMedGoogle Scholar
- Gilland DR, Jaszczak RJ, Bowsher JE, Turkington TG, Liang Z, Greer KL, Coleman RE: Quantitative SPECT brain imaging: effects of attenuation and detector response. IEEE Trans Nucl Sci 1993, 40: 295–299. 10.1109/23.221054View ArticleGoogle Scholar
- Tsui BMW, Frey EC, Zhao X, Lalush DS, Johnston RE, McCartney WH: The importance and implementation of accurate 3D compensation methods for quantitative SPECT. Phys Med Biol 1994, 39: 509–530. 10.1088/0031-9155/39/3/015View ArticlePubMedGoogle Scholar
- Tsui BMW, Zhao X, Frey EC, McCartney WH: Quantitative single-photon emission computed tomography: basics and clinical considerations. Semin Nucl Med 1994, 24: 38–65. 10.1016/S0001-2998(05)80248-XView ArticlePubMedGoogle Scholar
- Willowson K, Bailey DL, Bailey EA, Baldock C, Roach PJ: In vivo validation of quantitative SPECT in the heart. Clin Physiol Funct Imaging 2010, 30: 214–219. 10.1111/j.1475-097X.2010.00930.xView ArticlePubMedGoogle Scholar
- Zeintl J, Vija AH, Yahil A, Hornegger J, Kuwert T: Quantitative accuracy of clinical 99m Tc SPECT/CT using ordered-subset expectation maximization with 3-dimensional resolution recovery, attenuation, and scatter correction. J Nucl Med 2010, 51: 921–928. 10.2967/jnumed.109.071571View ArticlePubMedGoogle Scholar
- Israel O, Front D, Hardoff R, Ish-Shalom S, Jerushalmi J, Kolodny GM: In vivo SPECT quantitation of bone metabolism in hyperparathyroidism and thyrotoxicosis. J Nucl Med 1991, 32: 1157–1161.PubMedGoogle Scholar
- Ping HS, Kandaiya S: The influence of the patient size and geometry of cone beam-computed tomography Hounsfield unit. J Med Phys 2012,37(3):155–158. 10.4103/0971-6203.99239View ArticlePubMedGoogle Scholar
- Vija AH, Rempel TD, Hawman EG, Engdahl JC: Method to minimize dose for CT attenuation correction in SPECT. In Nuclear Science Symposium Conference Record 2004 (NSS ’04). Piscataway, NJ: IEEE; 2004:2929–2933.View ArticleGoogle Scholar
- Söderberg M, Gunnarsson M: The effect of different adaptation strengths on image quality and radiation dose using Siemens Care Dose 4D. Radiat Prot Dosimetry 2010,139(1–3):173–179.View ArticlePubMedGoogle Scholar
- Vija AH, Hawman EG, Engdahl JC: Analysis of a SPECT OSEM reconstruction method with 3D beam modeling and optional attenuation correction: phantom studies. In Nuclear Science Symposium Conference Record 2003 (NSS ’03). Piscataway, NJ: IEEE; 2003:2662–2666.Google Scholar
- Römer W, Reichel N, Vija AH, Nickel I, Hornegger J, Bautz W, Kuwert T: Isotropic reconstruction of SPECT data using OSEM3D: correlation with CT. Acad Radiol 2006, 13: 496–502. 10.1016/j.acra.2005.12.004View ArticlePubMedGoogle Scholar
- DuBois D, DuBois EF: A formula to estimate the approximate surface area if height and weight be known. Arch Int Med 1916, 17: 863–871.View ArticleGoogle Scholar
- Hallynck TH, Soep HH, Thomis JA, Boelaert J, Daneels R, Dettli L: Should clearance be normalised to body surface or to lean body mass? Br J Clin Pharmacol 1981, 11: 523–526. 10.1111/j.1365-2125.1981.tb01163.xView ArticlePubMedGoogle Scholar
- Zeintl J, Vija AH, Yahil A, Ding X, Hornegger J, Kuwert T: Towards quantitative SPECT: error estimation of SPECT OSEM with 3D resolution recovery, attenuation correction and scatter correction. In Nuclear Science Symposium Conference Record 2008 (NSS ’08). Piscataway, NJ: IEEE; 2008:4106–41011.View ArticleGoogle Scholar
- Willowson K, Bailey DL, Baldock C: Quantitative SPECT reconstruction using CT-derived corrections. Phys Med Biol 2008, 53: 3099–3112. 10.1088/0031-9155/53/12/002View ArticlePubMedGoogle Scholar
- Seret A, Nguyen D, Bernard C: Quantitative capabilities of four state-of-the-art SPECT-CT cameras. Eur J Nucl Med Mol Imaging Research 2012,2(45):1–19.Google Scholar
- Fogelman I, Bessent RG, Turner JG, Citrin DL, Boyle IT, Greig WR: The use of whole-body retention of Tc-99m diphosphonate in the diagnosis of metabolic bone disease. J Nucl Med 1978,19(3):270–275.PubMedGoogle Scholar
- Buell U, Kleinhans E, Zorn-Bopp E, Reuschel W, Muenzing W, Moser EA, Seiderer M: A comparison of bone imaging with Tc-99m DPD and Tc-99m MDP: concise communication. J Nucl Med 1982,23(3):214–217.PubMedGoogle Scholar
- Littlefield JL, Rudd TG: Tc-99m hydroxymethylene diphosphonate and Tc-99m methylene diphosphonate: biological and clinical comparison: concise communication. J Nucl Med 1983, 24: 463–466.PubMedGoogle Scholar
- Weber DA, Makler PT, Watson EE, Coffey JL, Thomas SR, London J: Radiation absorbed dose from technetium-99m-labeled bone imaging agents. J Nucl Med 1989, 30: 1117–1122.PubMedGoogle Scholar
- Kak AC, Slaney M: Principles of Computerized Tomographic Imaging. Philadelphia: Society of Industrial and Applied Mathematics; 2001.View ArticleGoogle Scholar
- Frost ML, Blake GM, Park-Holohan SJ, Cook GJ, Curran KM, Marsden PK, Fogelman I: Long-term precision of 18F-fluoride PET skeletal kinetic studies in the assessment of bone metabolism. J Nucl Med 2008, 49: 700–707. 10.2967/jnumed.107.046987View ArticlePubMedGoogle Scholar
- Segall G, Delbeke D, Stabin MG, Even Sapir E, Fair J, Sajdak R, Smit GT: SNM practice guideline for sodium 18F-fluoride PET/CT bone scans 1.0. J Nucl Med 2010,54(11):1813–1820.View ArticleGoogle Scholar
- Schwartz Z, Shani J, Soskolne WA, Touma H, Amir D, Sela J: Uptake and biodistribution of technetium-99m-MD 32 P during rat tibial bone repair. J Nucl Med 1993, 34: 104–108.PubMedGoogle Scholar
- Toegel S, Hoffmann O, Wadsak W, Ettlinger D, Mien LK, Wiesner K, Nquemo J, Viernstein H, Kletter K, Dudczak R, Mitterhauser M: Uptake of bone-seekers is solely associated with mineralization: a study with 99m Tc-MDP, 153 Sm-EDTMP and 18 F-fluoride on osteoblasts. Eur J Nucl Med 2006, 33: 491–494. 10.1007/s00259-005-0026-xView ArticleGoogle Scholar
- Genant HK, Engelke K, Prevrhal S: Advanced CT bone imaging in osteoporosis. Rheumatology 2008,47(Suppl 4):iv9-iv16.PubMedGoogle Scholar
- Engelke K, Kemmler W, Lauber D, Beeskow C, Pintag R, Kalender WA: Exercise maintains bone density at spine and hip EFOPS: a 3-year longitudinal study in early postmenopausal women. Osteoporos Int 2006, 17: 133–142. 10.1007/s00198-005-1938-9View ArticlePubMedGoogle Scholar
- Blain H, Chavassieux P, Portero-Muzy N, Bonnel F, Canovas F, Chammas M, Maury P, Delmas PD: Cortical and trabecular bone distribution in the femoral neck in osteoporosis and osteoarthritis. Bone 2008, 43: 862–868. 10.1016/j.bone.2008.07.236View ArticlePubMedGoogle Scholar
- Engelke K, Adams JE, Armbrecht G, Augat P, Bogado CE, Bouxsein ML, Felsenberg D, Ito M, Prevrhal S, Hans DB, Lewiecki EM: Clinical use of quantitative computed tomography and peripheral quantitative computed tomography in the management of osteoporosis in adults: the 2007 ISCD official positions. J Clin Densitom 2008,11(1):123–162. 10.1016/j.jocd.2007.12.010View ArticlePubMedGoogle Scholar
- Eisenhauer EA, Therasse P: New response evaluation criteria in solid tumours: revised RECIST guideline (version 1.1). Eur J Cancer 2009,45(2):228–247. 10.1016/j.ejca.2008.10.026View ArticlePubMedGoogle Scholar
- Cook GJR, Blake GM, Marsden PK, Cronin B, Fogelman I: Quantification of skeletal kinetic indices in Paget’s disease using dynamic 18 F-fluoride positron emission tomography. J Bone Miner Res 2002,17(5):854–859. 10.1359/jbmr.2002.17.5.854View ArticlePubMedGoogle Scholar
- Zeintl J, Vija AH, Yahil A, Hornegger J, Kuwert T: Quantitative accuracy of slow-rotating dynamic SPECT. In Nuclear Science Symposium Conference Record 2009 (NSS ’09). Piscataway: IEEE; 2009:3853–3857.View ArticleGoogle Scholar
- Hyldstrup L, McNair P, Ring P, Henriksen O: Studies on diphosphonate kinetics. Eur J Nucl Med 1987,12(12):581–588. 10.1007/BF00284529View ArticlePubMedGoogle Scholar
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