Introduction
Rheumatoid arthritis (RA) is one of the most common autoimmune diseases, affecting approximately 1% of the population in Europe and North America. Bone erosion can be detected as early as several weeks after the onset of the first clinical signs and symptoms of RA[
1]. Pathogenesis in preclinical models is similar to that in clinical RA; it is characterized by inflammation and bone destruction. In the past few decades, histopathological evaluation of joint sections has mainly been used for assessment of inflammation and bone destruction in small-rodent models of arthritis. Recently, we showed the benefit of state-of-the-art imaging modalities for visualization and quantitative assessment of inflammation in glucose-6-phosphate isomerase (G6PI)–induced arthritis using 2-deoxy-2-
18 F-fluoroglucose (
18 F-FDG) positron emission tomography/computed tomography (PET/CT)[
2]. Also, it has been shown that cell proliferation can be detected in experimental arthritis with the PET proliferation tracer 3′-deoxy-3′-
18 F-fluorothymidine[
3].
18 F-fluoride not only can be used to label glucose and other molecules of physiologic relevance but also has favorable properties in the form of sodium
18 F-fluoride (
18 F-NaF) as a radiotracer
per se in noninvasive
in vivo imaging to investigate musculoskeletal diseases[
4]. The use of
18 F-NaF as a bone imaging probe was established by Blau
et al. in the early 1960s[
5], but it was subsequently replaced by
99mTc-labeled tracers due to their availability, lower costs and the lower energy of 140-keV photons, allowing the use of γ-cameras.
18 F-fluoride PET is an increasingly used molecular imaging modality, not only in human skeletal disorders but also in small-animal preclinical research[
6‐
8]. This is facilitated by the distribution and use of three-dimensional PET scanners with high spatial resolution in clinical medicine and advantages over
99mTc-labeled bone agents used for skeletal scintigraphy, such as higher diagnostic accuracy and reduced scanning time. Compared to γ-cameras, molecular imaging using PET provides the advantages of higher spatial resolution, higher sensitivity and three-dimensional tomographic image reconstruction. Furthermore, the combination of PET with μCT enables attenuation correction of radiotracer signaling, allowing quantitative measurements using
18 F-fluoride PET/CT.
Applied
18 F-NaF, dissociated into Na
+ and
18 F
−, is rapidly cleared from the blood and accumulates in the bone, where, on the hydroxyapatite surface, an OH
− ion is replaced by an
18 F
− ion to form fluorapatite. The incorporation of
18 F-fluoride in the bone is determined by vascular perfusion and bone surface accessible for ion exchange, indirectly reflecting bone formation and bone resorption[
9]. This means that
18 F-NaF can be used not only for the common measurement of bone mineral deposition but also for visualization of osteolytic increases of exposed bone surface, such as in the context of musculoskeletal autoimmune disease[
10].
In clinical oncology, primary bone tumors and skeletal metastasis can reliably be detected by
18 F-fluoride PET[
4,
11]. In mice, pathological osteoblastic activity can be detected even earlier by
18 F-fluoride PET/CT imaging than by radiography and corresponds to histological evaluation of increased bone formation[
7]. As with bone tumor pathogenesis, a pathologically increased bone metabolism is a central feature of chronic arthritis, resulting in functional disorders of the joints[
12]. Therefore, in our present study, we examined the use of
18 F-NaF small-animal PET/CT for the quantitative and noninvasive
in vivo assessment of pathophysiological bone metabolism in acute and chronic stages of experimental G6PI-induced murine arthritis.
18 F-NaF PET quantification of bone destruction, visible as lesions in cortical bone surface and dysregulated bone formation, was validated using high-resolution CT measurements of the paws.
Methods
Glucose-6-phosphate isomerase–induced arthritis
DBA/1 mice were bred at the animal facility of the Jena University Hospital (Jena, Germany). All animal studies were approved by the local commission for animal protection (Thüringer Landesamt für Verbraucherschutz, Bad Langensalza, Germany; registered number 02-045/08). Arthritis was induced as described elsewhere[
13]. In brief, DBA/1 mice were immunized subcutaneously with 400 μg of recombinant human G6PI in emulsified complete Freund’s adjuvant (Sigma-Aldrich, Taufkirchen, Germany). Macroscopic evaluation of arthritis was performed according to severity of clinical manifestations in wrist and ankle joints, in metacarpophalangeal and metatarsophalangeal joints, and in digits and toes. Swelling and redness in wrist and ankle joints and in metacarpophalangeal and metatarsophalangeal joints, respectively, were graded from 0 to 3. A score of 0 indicates no macroscopically recognizable signs of arthritis, 1 indicates swelling and redness, 2 means strong swelling and redness and 3 indicates massive swelling and redness. Additionally, the number of digits and toes with inflamed joints were divided in half to avoid assessment imbalance because inflammation in the G6PI-induced arthritis model is located mainly in proximal joints of the paws[
2]. To calculate the total clinical score per animal, results from all paws were summed. For PET/CT measurements, mice were anesthetized with 1.5% to 2% isoflurane (Deltaselect, Dreieich, Germany) vaporized in oxygen (1.5 L/min) to prevent animal movement and reduce imaging artifacts. Respiration of mice under anesthesia was monitored.
18 F-fluoride (half-life = 109 minutes; Eckert & Ziegler, Bad Berka, Germany) with an activity of 10.4 ± 0.8 MBq was injected intravenously into the lateral tail vein. Longitudinal arthritis imaging was performed at various time points of acute and chronic clinical arthritis (
n = 3 to 6 mice per time point). We obtained dynamic PET scans for kinetic analysis of tracer uptake in nonimmunized mice (
n = 3).
Positron emission tomography/computed tomography in vivo imaging
In vivo18 F-NaF imaging was performed using a Siemens Inveon small-animal multimodality PET/CT system (Preclinical Solutions, Siemens Healthcare Molecular Imaging, Knoxville, TN, USA), characterized by the combination of two independently operating PET and CT scanners. Radial, tangential and axial resolutions at the center of the field of view of the PET module are 1.5 mm for this imaging modality[
14,
15]. PET image acquisition was carried out with a coincidence timing window of 3.4 ns and an energy window of 350 to 650 keV. PET data acquisition was performed for 1,800 seconds, starting 50 minutes after tracer application. In kinetic analysis, PET data acquisition lasted 5,400 seconds and started concomitantly with radiotracer injection. Images were reconstructed into three-dimensional images using Fourier rebinning and three-dimensional ordered-subset expectation maximization algorithm. Attenuation of PET data was corrected based on the CT measurements. The CT module consists of a cone-beam X-ray μCT source (50-μm focal spot size) and a 3,072 × 2,048–pixel X-ray detector. In our μCT imaging protocol, we used an axial–transaxial resolution of 2,048 × 2,048–pixel, 80 kVp at 500 μA, 360° rotation and 360 projections per bed position for paw measurements and 3,072 × 2,048–pixel, 220° rotation and 120 projections per bed position for whole-animal attenuation scans, respectively. CT images were reconstructed using a Shepp-Logan filter and cone-beam–filtered back projection. To reduce stress due to overly prolonged measurement times, only high-resolution μCT data from hindpaws were acquired for correlation analysis of bone surface assessment with
18 F-fluoride PET and CT.
Assessment of pathophysiological bone metabolism with 18 F-fluoride or μCT
Quantitative analysis of 18 F-fluoride accumulation in the period from 50 to 80 minutes after 18 F-fluoride injection or 0 to 90 minutes, respectively, was enabled by image fusion technology in Siemens Inveon Research Workplace 4.0 software. For dynamic PET analysis, scans were started 5 seconds before radiotracer injection and continued for 90 minutes. The 90-minute data set was divided into 45 time frames (6 × 10 seconds, 6 × 20 seconds, 7 × 60 seconds, 10 × 120 seconds, 10 × 180 seconds and 6 × 300 seconds) during histogramming to construct time–activity curves. For static analysis, data from 75 to 80 minutes after 18 F-fluoride injection were analyzed in a single time frame. Radioisotope activity in the venous blood pool or in fore- or hindpaws, reflecting bone incorporation of 18 F-fluoride, was measured as standardized uptake value (SUV; g/ml) using PMOD 3.15 software (PMOD Technologies Ltd, Zurich, Switzerland) or Siemens Inveon Research Workplace 4.0 software. Guided by maximum intensity projection images, volumes of interest were drawn as spheres (ellipsoids) over anatomic structures of bones and joints. A threshold of 40% (max–min) was used to separate the site of tracer accumulation from background tissue signaling. Visualization of skeletal elements of the hindpaws was also done using PMOD 3.15 software.
Analyses of metatarsal CT data were performed using Definiens Developer XD™ 2.0.3 build 2015 software (Definiens, Munich, Germany). For segmentation of metatarsal bones, the automatic threshold routine was used. Then, individual bones were discriminated by watershed segmentation. Oversegmented fragments were merged manually to achieve three-dimensional objects of each bone. After identification of metatarsals 1 to 5, a local threshold was applied on each metatarsal bone to refine bone margins and remove remaining nonbone pixels. The threshold was calculated as the difference between mean pixel gray value and standard deviation of pixel gray values. Quantitative measurements of bone surface and bone volume were calculated for each metatarsal bone.
Statistical analysis
Statistical differences between groups were evaluated using the nonparametric Mann-Whitney U test. Correlation analyses (Spearman test) were performed for PET data and clinical scoring or PET and CT data, respectively, whereas CT surface data of all metatarsals, per paw, were summed. Statistical significance was accepted at P < 0.05 (*P < 0.05, **P < 0.01, ***P < 0.001). In bar charts and text, data are given as arithmetic means and standard errors of the mean (SEM). All calculations were performed using the software package IBM SPSS Statistics version 20.0 (IBM, Ehningen, Germany).
Discussion
The usefulness of the small-animal PET/CT imaging modality using
18 F-NaF as a radiotracer is not restricted to the detection of primary bone tumors and skeletal metastasis in cancer research.
18 F-fluoride PET/CT imaging is also a valid technique for use in the assessment of disease severity according to pathological bone turnover in the field of preclinical arthritis research. In this study, in which we employed the G6PI-induced arthritis model, we focused on the feasibility of using
18 F-fluoride PET to visualize and quantify pathological bone metabolism in distal murine arthritic joints noninvasively and
in vivo. In addition to joint inflammation, which can easily be quantified by
18 F-FDG PET/CT according to activation and proliferation of resident cells and migrated cells of the immune system, bone damage is the second major parameter used for assessment of arthritis severity[
2].
In contrast to 18 F-FDG, which is trapped in cells at sites of inflammation due to pathologically increased glucose metabolism, 18 F-fluoride represents for specific radiotracer accumulation in the bone. Erosive processes degrading bone and cartilage and dysfunctional bone repair mechanisms in RA and its animal models are associated with an increased bone surface. Therefore, the increased mineral-binding capacity results in site-specific 18 F-fluoride uptake in arthritic joints, which can easily be used for visualization and, more importantly, provides a measurement method for the quantification of pathological bone metabolism in preclinical arthritis models. The results of our studies show increased uptake of 18 F-fluoride in the paws of arthritic mice and reveal that the 18 F-fluoride PET/CT quantification of pathologic bone metabolism in arthritis pathogenesis significantly correlated with our assessment of pathophysiologic bone surface alterations based on high-resolution μCT measurements.
Radioisotope imaging is, to date, one of the most applicable imaging modalities for functional and whole-body
in vivo quantification of bone metabolism in mice. Compared to other radiopharmaceuticals used for bone imaging, such as
99mTc,
18 F-fluoride has some beneficial attributes. First,
18 F-fluoride has a high affinity to bone, resulting in favorable skeletal kinetics. Within 60 minutes after intravenous injection, only 10% of the injected dose is still located in the bloodstream[
10]. Thus the concurrence of rapid bone uptake and fast blood-pool clearance yields a favorable bone-to-background ratio. Additionally,
18 F-fluoride does not accumulate in inflamed soft tissue and only minimally binds to serum proteins[
16]. Furthermore, small-animal
18 F-NaF PET measurements have an excellent reproducibility in animal models of bone disease[
6,
17].
One limiting factor in
18 F-fluoride PET imaging might be vascularization of the tissue restricting tracer delivery. In contrast to epithelial tissue, the circulation in well-vascularized bone tissue is less affected by exogenous factors, allowing reproducible data acquisition. In experimental arthritis, the increased vascularization and blood flow in inflamed tissue may influence tracer delivery and, therefore, PET signaling at stages of acute inflammation. Nevertheless, at time points of maximal tracer uptake in our experiments, clinical arthritis was already remitting and macroscopically visible signs of inflammation were diminished. Another important aspect of
18 F-fluoride PET imaging is bone structure. Skeletal elements consisting of cortical and trabecular bone result in strong baseline PET signaling. This is presumably caused by the manifold increase in bone surface and less by increased metabolism at these sites, as binding capacities of cortical and trabecular bone are only slightly different. However, both decrease significantly if bone matrix is demineralized[
18]. Therefore, if bones with cancellous and noncancellous structures are located near regions of interest, data analyses require a high degree of anatomical accuracy, which can be achieved with μCT. In quantification of experimental arthritis severity, we found that the effect of high baseline signaling in tibial and radial bones was of negligible relevance for
18 F-fluoride PET imaging, because signaling hotspots of arthritis pathogenesis were located in tarsal, metatarsal and carpal and metacarpal bones. Another source of a high and pathological
18 F-fluoride baseline PET signaling independent of autoimmune disease pathogenesis might be the preoccurrence of osteoarthritis resulting in mechanical bone erosion. Whereas this aspect is not relevant for imaging in experimental arthritis models, it should be considered in RA bone imaging, where age is a risk factor.
Conclusion
In our present study, we demonstrate the capability of 18 F-fluoride PET to monitor and quantify pathological bone conditions in the model of G6PI-induced arthritis. Furthermore, we validated this bone imaging technique successfully by using bone surface μCT data. Because 18 F-fluoride PET is a noninvasive and nondestructive way to measure bone metabolism in vivo, this molecular imaging modality is not only useful for numerous applications in basic animal science, where pathophysiological bone metabolism is of interest, but also is a valuable tool for use in preclinical arthritis research, where pathological bone destruction and inflammation are the major parameter used for assessment of disease severity.
Competing interests
The authors declare that they have no competing interests.
Authors’ contributions
II was responsible for study conception and design, animal experiments and data collection, PET data analysis and interpretation and manuscript writing. PG was responsible for study design, animal experiments and data collection, PET data analysis and manuscript writing. TO was responsible for animal experiments and data collection and PET data analysis. BH and MF were responsible for μCT data analysis and interpretation. HS and TK were responsible for data interpretation and critical revision of manuscript. All authors read and approved the final version of the manuscript.