- Original research
- Open Access
FIBT versus florbetaben and PiB: a preclinical comparison study with amyloid-PET in transgenic mice
© Hooshyar Yousefi et al.; licensee Springer. 2015
Received: 7 November 2014
Accepted: 22 February 2015
Published: 28 March 2015
Over the last decade, an increasing number of studies have been published on the use of amyloid-β (Aβ) PET imaging with different 18F-radiopharmaceuticals for clinical characterization of Alzheimer’s disease (AD) in different stages. However, distinct study cohorts and different quantification techniques allow only for an indirect comparison between the different tracers. Thus, the aim of this study was the direct intra-individual in vivo comparison of different Aβ-targeted radiopharmaceuticals for PET imaging, including the newly developed agent [18F]FIBT.
A small group of four animals of a well-characterized APP/PS1 transgenic (tg) mouse model of AD and gender-matched control (ctl) animals underwent a sequential and standardized PET imaging regimen for direct comparison of [18F]FIBT, [18F]florbetaben, and [11C]PiB. The quantitative PET imaging data were cross-validated with the cerebral Aβ plaque load as quantified ex vivo on histological sections.
We found that FIBT (2-(p-methylaminophenyl)-7-(2-[18F]fluoroethoxy)imidazo[2,1-b]benzothiazole) compares favorably to florbetaben as a high-contrasting PET radiopharmaceutical for imaging Aβ pathology. The excellent pharmacokinetics of FIBT in combination with its high-binding affinity towards Aβ resulted in feasible high-contrast imaging of Aβ with high global cortex to cerebellum standard uptake value ratio (SUVR) in 24-month-old tg mice (tg 1.68 ± 0.15 vs. ctl 0.95 ± 0.02). The SUVRs in transgenic versus control animals (SUVRtg/SUVRctl) for FIBT (1.78 ± 0.16) were similar to the ratios as observed in humans (SUVRAD/SUVRctl) for the established gold standard Pittsburgh compound B (PiB) (1.65 ± 0.41).
This head-to-head PET tracer comparison study in mice indicated the good imaging properties of [18F]FIBT, such as high initial brain uptake, fast clearance of the brain, and high binding affinity towards Aβ as directly compared to the established amyloid tracers. Moreover, the preclinical study design is recommendable for reliable assessment and comparison of novel radiopharmaceuticals.
Amyloid-β (Aβ) PET has become an important research biomarker for diagnosing and differentiating neurodegenerative disorders, in particular Alzheimer’s disease (AD). In the last decade, major efforts to develop and assess radiopharmaceuticals for early visualization and quantification of Aβ deposits with PET have been reported [1-3]. These endeavors were related to the amyloid cascade hypothesis which assumes that fibrillar Aβ is one of the key pathogenic hallmarks of AD [4-6], therefore, it has been depicted as major target for non-invasive diagnosing of AD. They have resulted in a variety of newly developed radiopharmaceuticals which have been assessed in preclinical and clinical studies [7-10]. Currently, three 18F-labeled PET radiopharmaceuticals for Aβ have been evaluated in clinical studies and are now approved by the United States Food and Drug Administration (FDA) and by the European Medicines Agency (EMA): flutemetamol [11,12], florbetaben [13-15], and florbetapir [16-24]. At least two other tracers are already undergoing clinical investigation [25,26]. In our lab, a new series of Aβ ligands, imidazo[2,1-b]benzothiazole (IBT), has been developed inspired by positive imaging results obtained in the IMPY and Pittsburgh compound B (PiB) studies. The IBT structural motifs share features with IMPY and PiB. Furthermore, it also allows stable 18F-fluorination. Our aim was to develop a more sensitive Aβ ligand that is easy to synthesize and therefore allows early and practicable detection of amyloid deposition [25,27,28]. With several 18F-labeled tracers competing, comparative conclusions are of high interest. However, most of the published studies so far have relied on different methodologies and cohorts, and a direct comparison and ranking in a clinical setting is challenging for their different characteristics . These limitations draw the attention to preclinical approaches for a direct intra-individual in vivo comparison of different 18F-labeled Aβ tracers.
Alongside tracer development advances subsequent to the application of PiB in a clinical setting , Aβ PET imaging was advanced with more sophisticated detection modes and highly sensitive detectors combined with powerful reconstruction and quantification algorithms . In addition, several transgenic animal models of AD have been established for preclinical evaluation of experimental treatments [32-34,10]. Aβ PET imaging in transgenic mouse models of AD is a powerful tool to assess Aβ tracer properties in vivo [27,35-38]. However, recent publications made it clear that the type of mouse model seems to play a crucial role as they differ in extent and type of Aβ pathology [39,35]. A new APP/PS1 transgenic mouse model of AD, expresses mutant forms of human amyloid precursor protein (APP) and presenilin-1 (PS1), was characterized  in collaboration with our group for its application in Aβ imaging  and usage for the evaluation of new Aβ ligands [25,27,40]. For this mouse model, a linear relationship of Aβ plaque pathology and PiB PET signal was observed .
In order to estimate the translational value of the preclinical results, we compared [11C]PiB standard uptake value ratio (SUVR) values from our APP/PS1 and control mice with human [11C]PiB SUVR values from 20 AD patients and 15 healthy elderly volunteers.
Animal experiments were carried out with the approval of the institutional animal care committee (Regierung von Oberbayern, München, Germany) and in accordance with the German Animal Welfare Act. Animal husbandry followed the regulations of the European Union (EU) guideline no. 2010/63. All imaging experiments were performed with male mice: four homozygous APP/PS1 mice ((B6;CB-Tg(Thy1-Psen1*M146V/Thy1-APP*swe)-10Arte), TaconicArtemis GmbH, Cologne, Germany) on a congenic C57BL/6 J genetic background and three age-matched control mice (C57BL/6 J). Mean age and mean weight: 23.8 ± 0.4 months and 33.3 ± 3.2 for APP/PS1 mice (tg) and 24.6 ± 0.4 months and 38.8 ± 2.6 g for C57BL/6 J control mice (ctl), respectively. For biodistribution studies, BALB/c mice were obtained from Charles River Laboratories, Sulzfeld, Germany.
Human data comes from preexisting studies at the Department of Nuclear Medicine with subjects who were recruited from the outpatient memory clinic of the Department of Psychiatry at the Technische Universität München (TUM). They had been referred for the diagnostic evaluation of cognitive impairment by general practitioners, neurologists, psychiatrists, or from other institutions. They underwent a standardized diagnostic protocol. All examinations were part of their routine check-up in the course of the evaluation of the patient’s neurodegenerative disorders. The psychometric workup was based on the Consortium to Establish a Registry for AD (CERAD) neuropsychological battery, which includes the Mini-Mental-State Examination (MMSE). All patients provided a written informed consent regarding the scientific evaluation of their data.
All chemicals, solvents, and materials were purchased and directly used without further purification. [18F]florbetaben (8% ± 2% radiochemical yield (RCY) and 98% radiochemical purity) [43,44], [18F]FIBT (20% ± 4% RCY and 98% radiochemical purity) , and [11C]PiB (26% ± 5% RCY and 98% radiochemical purity) [45-47,27] were synthesized following already published procedures. Analytical HPLC was performed using either a Chromolith RP-C18e (4.6 × 100 mm; Merck, Dramstadt, Germany) eluted with a mixture of acetonitrile/0.1-M ammonium formate (MeCN content between 27.5% and 50%) at a flow rate of 5 mL/min or a Nucleosil 100, CN 4.6 × 250 mm reverse phase column, particle size 5 μm (CS-Chromatographie, Langerwehe, Germany) eluted with acetonitrile/0.1-M ammonium formate (MeCN content between 40% and 60%). Both chromatography systems were fitted with a UV detector (Sykam Model S3210 set at 254 nm; Sykam, Fürstenfeldbruck, Germany). Radiotracers had comparable specific activities of ≥18 GBq/μmol.
Lipophilicity (log D oct/PBS) measurements
Lipophilicity of the employed compounds was determined by a conventional partition method between 1-octanol and phosphate buffered saline (PBS), pH 7.4. The 1-octanol was saturated with PBS before use. Briefly, the no-carrier-added tracers, contained in 0.2 mL PBS, were added 0.2 mL of 1-octanol in a 1.5-mL polypropylene Eppendorf vial. The vial was sealed and vigorously shaken at room temperature for 5 min. The mixture was then centrifuged at 3,000 g for 10 min. A 100 μL aliquot from each of the two phases was drawn and their radioactivity content was determined in a NaI (Tl) well-type detector. The log D oct/PBS was calculated as follows: log D oct/PBS = log (radioactivity concentration in the 1-octanol phase/radioactivity concentration in the PBS phase). The reported values represent the mean of six independent measurements.
Brain uptake studies of FIBT, florbetaben, and PiB in BALB/c mice
Ex vivo brain uptake studies were performed in male BALB/c mice (mean ± SD body weight: 23 ± 2 g). Mice were injected via lateral tail vein with 4 to 6 MBq of high specific activity (≥11 GBq/μmol) [18F]FIBT, [18F]florbetaben, and [11C]PiB contained in 0.1 to 0.15 mL of a solution of isotonic phosphate buffered saline. Groups of mice were killed at 5 and 30 min p.i. Radioactivity of weighted brain samples was measured in a γ-counter (Wallac 1480-011 Automatic Gamma Counter, PerkinElmer, Waltham, MA, USA). Data are expressed as percent of the injected dose per gram tissue (% I.D./g; mean ± SD, N = 5).
Small animal PET
Inhalation anesthesia with isoflurane was used and the eyes of the animals were protected with dexpanthenol eye ointment. Anesthesia was initiated 15 min ahead of experiments by placing the animal in a cage ventilated with oxygen (3.5 L/min) containing 3% isoflurane. Throughout the experiments, anesthesia was maintained by adjusting the isoflurane content (0.6% to 2%) to ensure a respiratory rate in the range 80 to 100/min. For i.v. injection, we inserted a tailored catheter into the lateral tail vein. Simultaneously with a slow bolus injection of 50 to 200 μL of tracer solution, we started the PET with scan duration of 45 min in 3D list mode on a Siemens Inveon system (axial field-of-view of 12.7 cm with a bore diameter of 12 cm, approximately 1.4 mm full-width-at-half-maximum spatial resolution; Siemens Healthcare, Erlangen, Germany). After tracer injection, we flushed the catheter with 50 to 100 μL of isotonic sodium chloride solution. During the scan, a heating pad prevented hypothermia. The radioactivity in the syringe was measured immediately before and after injection with a Capintec CRC® 15R (Capintec Inc, 6 Arrow Road Ramsey, NJ, USA) dose calibrator.
Scanning regimen of PiB, FIBT, and florbetaben
Scanning regimen of [ 11 C]PiB, [ 18 F]FIBT, and [ 18 F]florbetaben
Injected dose (MBq)
Δ t to next scan (days)
Injected dose (MBq)
Δ t to next scan (days)
Injected dose (MBq)
MR imaging of mice
A brain MR scan was performed on all tg and ctl mice within 0 to 6 days after PET scans. Throughout the MR scan, animals were under continuous 1.0% to 1.8% isoflurane anesthesia with 2 L/min oxygen flow. Eyes were protected with dexpanthenol ointment. Hypothermia was prevented with a heat storing gel pack (ColdHot, 3 M, Saint Paul, MN, USA) preheated in a microwave oven.
We acquired T1 weighted brain images using a 3D turbo gradient echo (3D-TFE) sequence with an inversion pre-pulse (TR: 12 ms, TE: 3.9 ms, TI: 800 ms, TFE factor: 120, flip angle: 8°, NSA: 12, acquired matrix M × P: 248 × 120, partitions: 60, FOV: 64 × 32 × 16 mm, resolution: 0.26 × 0.27 × 0.26 mm, reconstructed resolution: 0.13× 0.13 × 0.13 mm) on a Philips Achieva 1.5 T clinical MRI system with a 23-mm microscopy coil. Acquisition time was 46 min 11 s.
Mouse PET and MRI
Based on our experience, variance of macroscopic brain anatomy is very low across mice with the same genetic background. Therefore, the creation of a MRI template was done by manual co-registration of all MR images based on prominent brain structures and the overall cortical contour and calculation of a mean image (Pmod 3.3, Pmod Technologies, Zurich, Switzerland). Structures outside of the brain were not considered in the manual co-registration process. Two major volume-of-interests (VOIs) were defined on the MRI template, one comprising the full cortex including hippocampus, the other comprising the full cerebellum. The same VOIs were then used for reading out co-registered PET data of a mean image of the final 10 min of the scan (minute 36 to 45). The VOIs were chosen based on previous findings in a voxel-based analysis of cerebral PiB uptake and its correlation with the underlying Aβ pathology in this mouse model . PET data was normalized and corrected for decay and dead time. The images were reconstructed by means of filtered back-projection (FBP), using a ramp filter with a cutoff at the Nyquist frequency into 45 frames (45 × 60 s). The image volume consisted of 128 × 128 × 159 voxels, each of a size of 0.78 × 0.78 × 0.80 mm. The PET images were manually co-registered with the MRI template. This was done by using the wash-in phase of the tracer to identify the brain contour for alignment with the MRI template. We scaled the PET images to percentage of injected dose per cubic centimeter. We then applied these VOIs to the co-registered PET images and exported the VOI values to Microsoft Excel 2010 in order to calculate cortex + hippocampus-to-cerebellum ratios (further referred to as PET ratios).
We tested the tg/ctl ratios for significance. First, we performed a one-way ANOVA between the three groups showing significance. Post hoc Bonferroni corrected t-tests thresholded at p < 0.05 revealed that the significant difference is due to group differences between PiB and florbetaben and FIBT and florbetaben.
Brain dissection and tissue section preparation
Immediately after the third PET scan, each animal was sacrificed per cervical dislocation. The skull was dissected and opened mid-sagittally with fine scissors. The brain was carefully removed, halved in the left and right hemisphere and frozen with fine crushed dry ice and stored in a refrigerator at −80°C. For histological staining, the right hemisphere of each animal was thawed, para-sagittal halved and paraffinated. The resulting paraffin blocks were then cut with a thickness of 5 μm and mounted 3 sections per glass slide.
Thioflavin S staining and microscopy
Before staining, the sections were deparaffinated and rehydrated. The sections were then incubated in a 1% (1 g per 100 ml water) solution of Thioflavin S (TfS) (T1892, Sigma-Aldrich, St. Louis, MI, USA) for 30 min. The sections were then washed with water three times for 2 min, 80% ethanol for 6 min, washed again with water and cover slip mounted with VectaShield as mounting medium (H-1500 with DAPI, Vector Laboratories Inc., Burlingame, CA, USA). The slides were stored at 4°C until microscopic image acquisition. Digital images were acquired with an automated whole-slide-scanner (Mirax Scan, Carl Zeiss MicroImaging GmbH, Jena, Germany) using filter sets for DAPI, GFP, and Texas Red. The DAPI (contained in the mounting medium) fluorescence was used by the scanner to set the optical focus, GFP contained the specific signal of Thioflavin S, and Texas Red delivered unspecific fluorescence such as tissue auto-fluorescence. Images were pre-processed with Photoshop CS4 in order to define (blue-channel) the cortex and hippocampus as regions of interest for plaque load analysis.
Histological plaque load analysis
To measure the relative plaque load in a region of interest (ROI) of each section, we used the AcapellaTM analysis software (PerkinElmer Inc., Waltham, MA, USA) applying a special script (developed by Evotec AG, Hamburg, Germany). This script allows quantitative assessment of the relative plaque load (sum of pixels representing plaque signals divided by the sum of all pixels representing the regions of interest). The Texas Red signal was used by AcapellaTM to correct the TfS signal for unspecific fluorescence.
Acapella analysis was verified on each section. Minor detection deficits were tolerated (e.g., failure to detect <5 plaques); larger deficits (e.g., failure to detect a group of plaques) lead to exclusion of the particular image. In cases of a large contamination detected as plaque-specific signal (e.g., a tissue fold or dust particle), the region of interest was adjusted. At least 8, maximal 12, sections per tg mouse per staining (respectively 3 to 6 sections per wild-type mouse) were analyzed and mean values of plaque load calculated per animal. Autoradiography (Additional file 1) was performed following procedures already reported .
Human [11C]PiB PET
To enable a comparison to human [11C]PiB PET data, we chose randomly PET datasets from our database of AD patients and healthy controls at TUM. Subjects labelled as AD subjects in this database had a positive PiB scan together with measurable cognitive deficits in neuropsychological testing fulfilling the criteria of dementia. This data had been obtained on a SIEMENS ECAT HR+ scanner (CTI, Knoxville, TN, USA) according to an established and published protocol. Mean global cortical PiB uptake relative to cerebellum expressed as SUVR was calculated in 20 AD patients and in 15 healthy human control subjects using a previously established VOI-based approach [48,49].
Comparison of fundamental characteristics
Log D oct/PBS values of tested compounds (mean ± SD; N = 6)
[ 11 C]PiB
[ 18 F]FIBT
[ 18 F]Florbetaben
Log D oct/PBS
1.50 ± 0.11
1.92 ± 0.06
1.58 ± 0.13
[18F]FIBT > [11C]PiB*
[18F]FIBT > [18F]florbetaben*
[18F]Florbetaben > [11C]PiB
Intra-individual comparison of FIBT, florbetaben, and PiB in mice
Mean PET ratios (SUVR ± SD) within the four APP/PS1 tg mice and the three control mice (C57BL6/J)
[ 18 F]FIBT
[ 18 F]Florbetaben
[ 11 C]PiB
APP/PS1 (N = 4)
1.68 ± 0.15
1.35 ± 0.06
2.08 ± 0.24
C57BL6/J (N = 3)
0.95 ± 0.02
0.90 ± 0.01
0.99 ± 0.06
1.78 ± 0.16
1.50 ± 0.06
2.11 ± 0.24
[18F]FIBT > [18F]florbetaben*
[11C]PiB > [18F]florbetaben*
[11C]PiB > [18F]FIBT
Post mortem plaque load analysis of APP/PS1 and ctl mice
Human in relation to small-animal PiB PET
Human in relation to mouse PET with [ 11 C]PiB
2.01 ± 0.29
2.08 ± 0.24
1.22 ± 0.12
0.99 ± 0.06
1.65 ± 0.41
2.11 ± 0.24
This study was motivated by the finding that despite a considerable number of 18F-labeled Aβ tracers that has been described, a final answer to the key question, which of these radiopharmaceuticals shows optimal properties, cannot be given on the basis of existing data. This is mainly due to the inhomogeneity of preclinical characterization methods applied, and further complicated by primarily ethical, but also financial and other practical restrictions of evaluating radiopharmaceuticals head-to-head in the same human subjects. In addition, it appears practically impossible to acquire enough preclinical data to enable a mutual comparison of every possible pair of tracers. As suggested previously , this situation could be circumvented by using [11C]PiB as common standard, which is recommendable due to the considerable body of knowledge already gained for this compound. Following this rationale, some of the upcoming 18F-labeled tracers have been compared to [11C]PiB [51,52]. Consequently, [11C]PiB PET results in mice and humans were also implemented in our study as an anchor point for comparison.
One previous paper compared two 18F-labeled Aβ tracers indirectly via two separate groups of AD patients with a [11C]PiB scan as link between the two groups . However, this type of indirect comparison requires large cohorts to establish a valid comparison via statistical analysis. In terms of preclinical studies, an intra-individual based comparison of candidate tracers would require a direct correlation of the signal with the individual plaque load of the animal. This is necessary because one has to consider that in small animal models of AD, the inter-subject plaque load is generally not constant, which applies also to our transgenic model . Hence, the most notable advantage of our intra-individual comparison approach is that it allows for drawing meaningful conclusions from smaller sample sizes (cohorts), thus resolving some ethical (cf. triple-R rule) and economical issues at the same time. Furthermore, a group of transgenic mice can, in principle, be used to compare even more than three Aβ tracers, which might prove a useful means of parallel Aβ tracer evaluation in future studies. Admittedly, a certain drawback of our protocol is that, in principle, absolute quantification of small animal PET signals requires complex image analysis steps. However, by calculating ROI ratios, we chose a straightforward approach, which is frequently applied in clinical as well as preclinical settings, and is widely considered to yield sufficiently precise data to enable meaningful conclusions. The linear association of PET ratios with plaque load for all three tracers in Figure 5 implies that calculating ROI ratios further supports this approach. With the possibility of subsequent ex vivo and histopathological analyses, the advantages of the preclinical approach presented here go far beyond merely circumventing challenges, such as ethical implications of repetitive scans in clinical studies.
We compared [18F]FIBT with [18F]florbetaben and [11C]PiB using small animal PET in aged transgenic APP/PS1 and control mice. The direct head-to-head PET comparison was supplemented by semi-automated histological plaque load analyses, using the brain material from the animals previously subjected to PET, and by ex vivo brain uptake kinetic analyses in a separate group of wild-type BALB/c mice. Pharmacokinetics of [18F]FIBT was superior to [18F]florbetaben which also resulted in better PET ratios (1.68 ± 0.15 versus 1.35 ± 0.06) in transgenic mice. However, PET ratios of both tracers correlated equally well with amyloid pathology.
Sufficient uptake in the brain and rapid wash-out of unbound tracer are important determinants of potential signal strength and sensitivity of a tracer. These pharmacokinetic properties are commonly assessed by post mortem determination of brain uptake kinetic analyses in healthy animals. At first glance, chemical properties of both 18F-labeled tracers meet the requirements for sufficient permeation of the blood-brain barrier, such as low molecular weight and medium lipophilicity . However, we noted a lower initial uptake and higher tracer retention at 30 min p.i. of [18F]florbetaben compared to [18F]FIBT in animals without Aβ pathology (BALB/c mice). Higher initial uptake could be attributed to the slightly lower lipophilicity of [18F]florbetaben (log D = 1.58 ± 0.13) compared to [18F]FIBT (log D = 1.92 ± 0.06) [53,54] but might also be related to presence of hydrogen bond donors and acceptors as well as a higher percentage of polar surface area. Higher retention of [18F]florbetaben is likely due to a higher degree of unspecific binding. Hence, the low amount of unspecific retention of [18F]FIBT represents a substantial improvement, because compared to [11C]PiB, most 18F-labeled AD tracers in advanced clinical trials show a higher tendency towards unspecific binding to the white matter in humans [52,55].
Comparison of PET images of AD and control mice indicated higher unspecific binding of [18F]florbetaben compared to [18F]FIBT, especially in subcortical regions (red arrow in Figure 2), which is equivalent to a higher Aβ sensitivity of the latter. This might pose an important advantage with respect to the potential role of Aβ PET imaging in the pre-symptomatic phase of the disease , which is considered to begin several years before symptom onset (accumulation of pathological aggregates), and is likely the favorable time window for anti-amyloid interventions .
Apart from pharmacokinetic properties and specificity of binding, Aβ affinity and selectivity determines the quality of a tracer. In a competitive binding assay versus [3H]PiB, FIBT showed high affinity to Aβ aggregates (K i = 2.1 ± 0.8 nM) . Furthermore, in vitro determination of binding affinities to Aβ aggregates, using post mortem AD brain homogenates, suggest a higher Aβ affinity of [18F]FIBT (K d = 0.7 ± 0.2 nM ) than [18F]florbetaben (K d = 6.70 ± 0.30 nM, ). These results are nicely corroborated by our in vivo data, as we found higher tracer retention for [18F]FIBT than [18F]florbetaben in Aβ-rich brain regions of APP/PS1 transgenic mice (Figure 4A2). Since specific binding of PiB to Aβ in this mouse model was demonstrated previously by in vitro, ex vivo, and in vivo experiments , we conclude that higher retention of [18F]FIBT in target regions corresponds to improved specificity of binding in vivo as well.
Furthermore, it was shown earlier that the cortex-to-cerebellum ratios of PiB correlate well with the absolute amount of Aβ in the cortex, the place where most of the Aβ deposits are found . Ratios of PiB in APP/PS1 transgenic mice closely resembled the ratios measured in our cohort of AD patients, further supporting the notion that our transgenic mouse model is suitable for PET imaging studies of Aβ pathology. Being aware that results from small animal experiments can usually not be directly translated to a clinical setting, we nevertheless hold the view that clinical properties of other tracers evaluated in the same setting could be predicted with certain accuracy. Thus, we assume that FIBT could perform very well in human as a promising diagnostic Aβ radiopharmaceutical and robust imaging tool with potential to become an earlier AD biomarker.
With an increasing number of 18F-labeled Aβ tracers, comparative studies are of high value for providing diagnostic and prognostic information and feasibility rankings. Despite general problems of transferability of preclinical results to clinical settings, our study suggests that small animal PET imaging using a suitable animal model combined with ex vivo and in vitro experiments is a practicable approach for comparative Aβ tracer assessment. Overall, all assessed tracers allowed high-contrast imaging of Aβ deposits in transgenic models of AD. Our results indicate a superior performance of [18F]FIBT relative to [18F]florbetaben regarding pharmacokinetics and specific binding affinity towards Aβ aggregates. These results support further evaluation of [18F]FIBT in human investigations.
The authors thank Heinz von der Kammer, Evotec AG Hamburg and Michael Schoor, Taconic Biosciences GmbH for provision of the APP/PS1 mice; Michael Herz and Reinhold Klitsch for producing radioisotopes; and Sybille Reder, Monika Beschorner, Andrea Alke, and Katharina McGuire for excellent support by animal experimental. We also acknowledge Johannes Notni for prompt proofreading of this manuscript. This work was supported by DFG HE 4560/1-3 and DFG RTG 1373, DFG DR 445/3-1, 4-1, ERC Grant MUMI - No. 294582 and the Research Training Group 1373.
- Watanabe H, Ono M, Kimura H, Kagawa S, Nishii R, Fuchigami T, et al. A dual fluorinated and iodinated radiotracer for PET and SPECT imaging of beta-amyloid plaques in the brain. Bioorg Med Chem Lett. 2011;21(21):6519–22. doi:10.1016/j.bmcl.2011.08.063.View ArticlePubMedGoogle Scholar
- Kung MP, Weng CC, Lin KJ, Hsiao IT, Yen TC, Wey SP. Amyloid plaque imaging from IMPY/SPECT to AV-45/PET. Chang Gung Med J. 2012;35(3):211–8.PubMedGoogle Scholar
- Swahn BM, Sandell J, Pyring D, Bergh M, Jeppsson F, Jureus A, et al. Synthesis and evaluation of pyridylbenzofuran, pyridylbenzothiazole and pyridylbenzoxazole derivatives as (18)F-PET imaging agents for beta-amyloid plaques. Bioorg Med Chem Lett. 2012;22(13):4332–7. doi:10.1016/j.bmcl.2012.05.011.View ArticlePubMedGoogle Scholar
- Hardy JA, Higgins GA. Alzheimer’s disease: the amyloid cascade hypothesis. Science. 1992;256(5054):184–5.View ArticlePubMedGoogle Scholar
- Hardy J, Selkoe DJ. The amyloid hypothesis of Alzheimer’s disease: progress and problems on the road to therapeutics. Science. 2002;297(5580):353–6. doi:10.1126/science.1072994.View ArticlePubMedGoogle Scholar
- Reitz C. Alzheimer’s disease and the amyloid cascade hypothesis: a critical review. Int J Alzheimers Dis. 2012;2012:369808. doi:10.1155/2012/369808.PubMed CentralPubMedGoogle Scholar
- Henriksen G, Yousefi BH, Drzezga A, Wester HJ. Development and evaluation of compounds for imaging of beta-amyloid plaque by means of positron emission tomography. Eur J Nucl Med Mol Imaging. 2008;35 Suppl 1:S75–81. doi:10.1007/s00259-007-0705-x.View ArticlePubMedGoogle Scholar
- Quigley H, Colloby SJ, O’Brien JT. PET imaging of brain amyloid in dementia: a review. Int J Geriatric Psychiatry. 2011;26(10):991–9. doi:10.1002/gps.2640.View ArticleGoogle Scholar
- Brockschnieder D, Schmitt-Willich H, Heinrich T, Varrone A, Gulyas B, Toth M, et al. Preclinical characterization of a novel class of 18F-labeled PET tracers for amyloid-beta. J Nuclear Med. 2012;53(11):1794–801. doi:10.2967/jnumed.112.104810.View ArticleGoogle Scholar
- Vlassenko AG, Benzinger TL, Morris JC. PET amyloid-beta imaging in preclinical Alzheimer’s disease. Biochim Biophys Acta. 2012;1822(3):370–9. doi:10.1016/j.bbadis.2011.11.005.View ArticlePubMed CentralPubMedGoogle Scholar
- Koole M, Lewis DM, Buckley C, Nelissen N, Vandenbulcke M, Brooks DJ, et al. Whole-body biodistribution and radiation dosimetry of 18 F-GE067: a radioligand for in vivo brain amyloid imaging. J Nucl Med. 2009;50(5):818–22. doi:10.2967/jnumed.View ArticlePubMedGoogle Scholar
- Nelissen N, Van Laere K, Thurfjell L, Owenius R, Vandenbulcke M, Koole M, et al. Phase 1 study of the Pittsburgh compound B derivative 18 F-flutemetamol in healthy volunteers and patients with probable Alzheimer disease. J Nuclear Med. 2009;50(8):1251–9. doi:10.2967/jnumed.109.063305.View ArticleGoogle Scholar
- Rowe CC, Ackerman U, Browne W, Mulligan R, Pike KL, O’Keefe G, et al. Imaging of amyloid beta in Alzheimer’s disease with 18 F-BAY94-9172, a novel PET tracer: proof of mechanism. Lancet Neurol. 2008;7(2):129–35. doi:10.1016/S1474-4422(08)70001-2.View ArticlePubMedGoogle Scholar
- O’Keefe GJ, Saunder TH, Ng S, Ackerman U, Tochon-Danguy HJ, Chan JG, et al. Radiation dosimetry of beta-amyloid tracers 11C-PiB and 18 F-BAY94-9172. J Nucl Med: official publication, Soc Nuclear Med. 2009;50(2):309–15. doi:10.2967/jnumed.108.055756.View ArticleGoogle Scholar
- Wang H, Shi H, Yu H, Jiang S, Tang G. Facile and rapid one-step radiosynthesis of [(18)F]BAY94-9172 with a new precursor. Nucl Med Biol. 2011;38(1):121–7. doi:10.1016/j.nucmedbio.2010.06.009.View ArticlePubMedGoogle Scholar
- Choi SR, Golding G, Zhuang Z, Zhang W, Lim N, Hefti F, et al. Preclinical properties of 18 F-AV-45: a PET agent for Abeta plaques in the brain. J Nucl Med. 2009;50(11):1887–94. doi:10.2967/jnumed.109.065284.View ArticlePubMed CentralPubMedGoogle Scholar
- Lin KJ, Hsu WC, Hsiao IT, Wey SP, Jin LW, Skovronsky D, et al. Whole-body biodistribution and brain PET imaging with [18F]AV-45, a novel amyloid imaging agent - a pilot study. Nucl Med Biol. 2010;37(4):497–508. doi:10.1016/j.nucmedbio.2010.02.003.View ArticlePubMedGoogle Scholar
- Wong DF, Rosenberg PB, Zhou Y, Kumar A, Raymont V, Ravert HT, et al. In vivo imaging of amyloid deposition in Alzheimer disease using the radioligand 18F-AV-45 (florbetapir [corrected] F 18). J Nuclear Med. 2010;51(6):913–20. doi:10.2967/jnumed.109.069088.View ArticleGoogle Scholar
- Yao CH, Lin KJ, Weng CC, Hsiao IT, Ting YS, Yen TC, et al. GMP-compliant automated synthesis of [(18)F]AV-45 (Florbetapir F 18) for imaging beta-amyloid plaques in human brain. Appl Radiat Isot. 2010;68(12):2293–7. doi:10.1016/j.apradiso.2010.07.001.View ArticlePubMedGoogle Scholar
- Carome M, Wolfe S. Florbetapir-PET imaging and postmortem beta-amyloid pathology. JAMA. 2011;305(18):1857. author reply −8. doi:10.1001/jama.2011.579.View ArticlePubMedGoogle Scholar
- Clark CM, Schneider JA, Bedell BJ, Beach TG, Bilker WB, Mintun MA, et al. Use of florbetapir-PET for imaging beta-amyloid pathology. JAMA. 2011;305(3):275–83. doi:305/3/275 [pii] 10.1001/jama.2010.2008.View ArticlePubMedGoogle Scholar
- Lister-James J, Pontecorvo MJ, Clark C, Joshi AD, Mintun MA, Zhang W, et al. Florbetapir f-18: a histopathologically validated Beta-amyloid positron emission tomography imaging agent. Semin Nucl Med. 2011;41(4):300–4. doi:10.1053/j.semnuclmed.2011.03.001.View ArticlePubMedGoogle Scholar
- Fleisher AS, Chen K, Liu X, Roontiva A, Thiyyagura P, Ayutyanont N, et al. Using positron emission tomography and florbetapir F 18 to image cortical amyloid in patients with mild cognitive impairment or dementia due to Alzheimer disease. Arch Neurol. 2011;68(11):1404–11. doi:10.1001/archneurol.2011.150.View ArticlePubMedGoogle Scholar
- Okamura N, Yanai K. Florbetapir (18F), a PET imaging agent that binds to amyloid plaques for the potential detection of Alzheimer’s disease. IDrugs. 2011;13(12):890–9.Google Scholar
- Yousefi BH, Drzezga A, von Reutern B, Manook A, Schwaiger M, Wester HJ, et al. A novel 18F-labeled imidazo[2,1-b]benzothiazole (IBT) for high-contrast PET imaging of β-amyloid plaques. ACS Med Chem Lett. 2011;2(9):673–7.View ArticlePubMed CentralPubMedGoogle Scholar
- Cselenyi Z, Jonhagen ME, Forsberg A, Halldin C, Julin P, Schou M, et al. Clinical validation of 18F-AZD4694, an amyloid-beta-specific PET radioligand. J Nuclear Med. 2012;53(3):415–24. doi:10.2967/jnumed.111.094029.View ArticleGoogle Scholar
- Yousefi BH, Manook A, Drzezga A, von Reutern B, Schwaiger M, Wester HJ, et al. Synthesis and evaluation of 11C-labeled imidazo[2,1-b]benzothiazoles (IBTs) as PET tracers for imaging beta-amyloid plaques in Alzheimer’s disease. J Med Chem. 2011;54(4):949–56. doi:10.1021/jm101129a.View ArticlePubMedGoogle Scholar
- Yousefi BH, Manook A, Grimmer T, Arzberger T, von Reutern B, Henriksen G et al. Characterization and first human investigation of FIBT, a novel fluorinated abeta plaque neuroimaging PET radioligand. ACS Chem Neurosci. 2015. doi:10.1021/cn5001827Google Scholar
- Landau SM, Thomas BA, Thurfjell L, Schmidt M, Margolin R, Mintun M, et al. Amyloid PET imaging in Alzheimer’s disease: a comparison of three radiotracers. Eur J Nucl Med Mol Imaging. 2014;41(7):1398–407. doi:10.1007/s00259-014-2753-3.View ArticlePubMedGoogle Scholar
- Mathis CA, Wang Y, Klunk WE. Imaging beta-amyloid plaques and neurofibrillary tangles in the aging human brain. Curr Pharm Des. 2004;10(13):1469–92.View ArticlePubMedGoogle Scholar
- Villain N, Chetelat G, Grassiot B, Bourgeat P, Jones G, Ellis KA, et al. Regional dynamics of amyloid-beta deposition in healthy elderly, mild cognitive impairment and Alzheimer’s disease: a voxelwise PiB-PET longitudinal study. Brain. 2012;135(Pt 7):2126–39. doi:10.1093/brain/aws125.View ArticlePubMedGoogle Scholar
- Gotz J, Ittner LM. Animal models of Alzheimer’s disease and frontotemporal dementia. Nat Rev Neurosci. 2008;9(7):532–44. doi:10.1038/nrn2420.View ArticlePubMedGoogle Scholar
- Willuweit A, Velden J, Godemann R, Manook A, Jetzek F, Tintrup H, et al. Early-onset and robust amyloid pathology in a new homozygous mouse model of Alzheimer’s disease. PLoS ONE. 2009;4(11):e7931. doi:10.1371/journal.pone.0007931.View ArticlePubMed CentralPubMedGoogle Scholar
- Svedberg MM, Rahman O, Hall H. Preclinical studies of potential amyloid binding PET/SPECT ligands in Alzheimer’s disease. Nucl Med Biol. 2012;39(4):484–501. doi:10.1016/j.nucmedbio.2011.10.007.View ArticlePubMedGoogle Scholar
- Snellman A, Lopez-Picon FR, Rokka J, Salmona M, Forloni G, Scheinin M, et al. Longitudinal amyloid imaging in mouse brain with 11C-PIB: comparison of APP23, Tg2576, and APPswe-PS1dE9 mouse models of Alzheimer disease. J Nuclear Med. 2013;54(8):1434–41. doi:10.2967/jnumed.112.110163.View ArticleGoogle Scholar
- Snellman A, Rokka J, Lopez-Picon FR, Eskola O, Wilson I, Farrar G, et al. Pharmacokinetics of 18F]flutemetamol in wild-type rodents and its binding to beta amyloid deposits in a mouse model of Alzheimer’s disease. Eur J Nucl Med Mol Imaging. 2012;39(11):1784–95. doi:10.1007/s00259-012-2178-9.View ArticlePubMedGoogle Scholar
- Brendel M, Delker A, Rotzer C, Boning G, Carlsen J, Cyran C, et al. Impact of partial volume effect correction on cerebral beta-amyloid imaging in APP-Swe mice using [18F]-florbetaben PET. NeuroImage. 2013;84C:843–53. doi:10.1016/j.neuroimage.2013.09.017.Google Scholar
- Rominger A, Brendel M, Burgold S, Keppler K, Baumann K, Xiong G, et al. Longitudinal assessment of cerebral beta-amyloid deposition in mice overexpressing Swedish mutant beta-amyloid precursor protein using 18F-florbetaben PET. J Nuclear Med. 2013;54(7):1127–34. doi:10.2967/jnumed.112.114660.View ArticleGoogle Scholar
- Maeda J, Ji B, Irie T, Tomiyama T, Maruyama M, Okauchi T, et al. Longitudinal, quantitative assessment of amyloid, neuroinflammation, and anti-amyloid treatment in a living mouse model of Alzheimer’s disease enabled by positron emission tomography. J Neurosci. 2007;27(41):10957–68. doi:10.1523/JNEUROSCI.0673-07.View ArticlePubMedGoogle Scholar
- Yousefi BH, Manook A, von Reutern B, Schwaiger M, Drzezga A, Wester HJ, et al. Development of an improved radioiodinated 2-phenylimidazo[1,2-a]pyridine for non-invasive imaging of amyloid plaques. Medchemcomm. 2012;3(7):775–9. doi:10.1039/C2md20115a.View ArticleGoogle Scholar
- von Reutern B, Grunecker B, Yousefi BH, Henriksen G, Czisch M, Drzezga A. Voxel-based analysis of amyloid-burden measured with [11C]PiB PET in a double transgenic mouse model of Alzheimer’s disease. Molecular Imaging Biol. 2013;15(5):576–84. doi:10.1007/s11307-013-0625-z.View ArticleGoogle Scholar
- Villemagne VL, Ong K, Mulligan RS, Holl G, Pejoska S, Jones G, et al. Amyloid imaging with [18F]florbetaben in Alzheimer disease and other dementias. J Nuclear Med. 2011;52(8):1210–7. doi:10.2967/jnumed.111.089730.View ArticleGoogle Scholar
- Patt M, Schildan A, Barthel H, Becker G, Schultze-Mosgau MH, Rohde B, et al. Metabolite analysis of [18F]florbetaben (BAY 94-9172) in human subjects: a substudy within a proof of mechanism clinical trial. J Radioanal Nucl Chem. 2010;284:557–62.View ArticleGoogle Scholar
- Barthel H, Gertz HJ, Dresel S, Peters O, Bartenstein P, Buerger K, et al. Cerebral amyloid-beta PET with [18F]florbetaben in patients with Alzheimer’s disease and healthy controls: a multicentre phase 2 diagnostic study. Lancet Neurol. 2011;10(5):424–35. doi:10.1016/S1474-4422(11)70077-1.View ArticlePubMedGoogle Scholar
- Henriksen G, Hauser AI, Westwell AD, Yousefi BH, Schwaiger M, Drzezga A, et al. Metabolically stabilized benzothiazoles for imaging of amyloid plaques. J Med Chem. 2007;50(6):1087–9. doi:10.1021/jm061466g.View ArticlePubMedGoogle Scholar
- Grimmer T, Tholen S, Yousefi BH, Alexopoulos P, Forschler A, Forstl H, et al. Progression of cerebral amyloid load is associated with the apolipoprotein E epsilon 4 genotype in Alzheimer’s disease. Biol Psychiatry. 2010;68(10):879–84. doi:10.1016/j.biopsych.2010.05.013.View ArticlePubMed CentralPubMedGoogle Scholar
- Forster S, Grimmer T, Miederer I, Henriksen G, Yousefi BH, Graner P et al. Regional expansion of hypometabolism in Alzheimer’s disease follows amyloid deposition with temporal delay. Biol Psychiatry. 2011. doi:10.1016/j.biopsych.2011.04.023Google Scholar
- Forster S, Grimmer T, Miederer I, Henriksen G, Yousefi BH, Graner P, et al. Regional expansion of hypometabolism in Alzheimer’s disease follows amyloid deposition with temporal delay. Biol Psychiatry. 2012;71(9):792–7. doi:10.1016/j.biopsych.2011.04.023.View ArticlePubMedGoogle Scholar
- Forster S, Yousefi BH, Wester HJ, Klupp E, Rominger A, Forstl H, et al. Quantitative longitudinal interrelationships between brain metabolism and amyloid deposition during a 2-year follow-up in patients with early Alzheimer’s disease. Eur J Nucl Med Mol Imaging. 2012;39(12):1927–36. doi:10.1007/s00259-012-2230-9.View ArticlePubMedGoogle Scholar
- Klunk WE, Mathis CA. The future of amyloid-beta imaging: a tale of radionuclides and tracer proliferation. Curr Opin Neurol. 2008;21(6):683–7. doi:10.1097/WCO.0b013e3283168e1a.View ArticlePubMed CentralPubMedGoogle Scholar
- Serdons K, Verduyckt T, Vanderghinste D, Cleynhens J, Borghgraef P, Vermaelen P, et al. Synthesis of 18F-labelled 2-(4′-fluorophenyl)-1,3-benzothiazole and evaluation as amyloid imaging agent in comparison with [11C]PiB. Bioorg Med Chem Lett. 2009;19(3):602–5. doi:10.1016/j.bmcl.2008.12.069.View ArticlePubMedGoogle Scholar
- Rowe CC, Pejoska S, Mulligan RS, Jones G, Chan JG, Svensson S, et al. Head-to-head comparison of 11C-PiB and 18F-AZD4694 (NAV4694) for beta-amyloid imaging in aging and dementia. J Nuclear Med. 2013;54(6):880–6. doi:10.2967/jnumed.112.114785.View ArticleGoogle Scholar
- Laruelle M, Slifstein M, Huang Y. Relationships between radiotracer properties and image quality in molecular imaging of the brain with positron emission tomography. Molecular imaging Biol. 2003;5(6):363–75.View ArticleGoogle Scholar
- Waterhouse RN. Determination of lipophilicity and its use as a predictor of blood-brain barrier penetration of molecular imaging agents. Molecular Imaging Biol. 2003;5(6):376–89.View ArticleGoogle Scholar
- Rowe CC, Villemagne VL. Amyloid imaging with PET in early Alzheimer disease diagnosis. Medl Clin North Am. 2013;97(3):377–98. doi:10.1016/j.mcna.2012.12.017.View ArticleGoogle Scholar
- Jack Jr CR, Holtzman DM. Biomarker modeling of Alzheimer’s disease. Neuron. 2013;80(6):1347–58. doi:10.1016/j.neuron.2013.12.003.View ArticlePubMed CentralPubMedGoogle Scholar
- Panza F, Solfrizzi V, Imbimbo BP, Tortelli R, Santamato A, Logroscino G. Amyloid-based immunotherapy for Alzheimer’s disease in the time of prevention trials: the way forward. Expert Rev Clin Immunol. 2014;10(3):405–19. doi:10.1586/1744666X.2014.883921.View ArticlePubMedGoogle Scholar
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