- Original research
- Open Access
Evaluation of the biodistribution and radiation dosimetry of the 18F-labelled amyloid imaging probe [18F]FACT in humans
© Shidahara et al.; licensee Springer. 2013
- Received: 23 January 2013
- Accepted: 8 April 2013
- Published: 24 April 2013
The biodistribution and radiation dosimetry of the 18F-labelled amyloid imaging probe ([18F] FACT) was investigated in humans.
Six healthy subjects (three males and three females) were enrolled in this study. An average of 160.8 MBq of [18F] FACT was intravenously administered, and then a series of whole-body PET scans were performed. Nineteen male and 20 female source organs, and the remainder of the body, were studied to estimate time-integrated activity coefficients. The mean absorbed dose in each target organ and the effective dose were estimated from the time-integrated activity coefficients in the source organs. Biodistribution data from [18F] FACT in mice were also used to estimate absorbed doses and the effective dose in human subjects; this was compared with doses of [18F] FACT estimated from human PET data.
The highest mean absorbed doses estimated using human PET data were observed in the gallbladder (333 ± 251 μGy/MBq), liver (77.5 ± 14.5 μGy/MBq), small intestine (33.6 ± 30.7 μGy/MBq), upper large intestine (29.8 ± 15.0 μGy/MBq) and lower large intestine (25.2 ± 12.6 μGy/MBq). The average effective dose estimated from human PET data was 18.6 ± 3.74 μSv/MBq. The highest mean absorbed dose value estimated from the mouse data was observed in the small intestine (38.5 μGy/MBq), liver (25.5 μGy/MBq) and urinary bladder wall (43.1 μGy/MBq). The effective dose estimated from the mouse data was 14.8 μSv/MBq for [18F] FACT.
The estimated effective dose from the human PET data indicated that the [18F] FACT PET study was acceptable for clinical purposes.
- Positron emission tomography
- Radiation dosimetry
- Amyloid imaging
- [18F] FACT
Amyloid beta imaging
Deposits of amyloid β (Aβ) plaque are one of the pathological observations in patients with Alzheimer's disease (AD); Aβ deposition progresses at an earlier point than the current clinical diagnostic point for this disease . For earlier diagnosis of AD and the evaluation of treatment efficacy, in vivo amyloid imaging using positron emission tomography (PET), which provides quantitation and visualisation of Aβ deposition in the brain, is useful. Therefore, several Aβ-binding probes dedicated for PET imaging have been developed [2, 3].
Most of these PET Aβ ligands are 11C-labelled compounds (physical half life (T 1/2), 20 min), and 18F-labelled agents are being increasingly investigated owing to their long half life (T 1/2, 109.7 min). The long T 1/2 of 18F enables several PET scans to be carried out from a single synthesis of labelled agent and also enables its commercial distribution to any PET facility. On the other hand, the longer the T 1/2 of the radioisotope gets, the greater is the radiation dose exposure for the PET subject for the same administered dose of radioligand.
Importance of radiation dosimetry
For subjects undergoing PET, internal radiation exposure is inevitable, and the radiation dose delivered is proportional to the level of radioactivity of the injected radioligand and the number of injections. In the case of amyloid imaging, subjects often have multiple PET scans for diagnostic or therapeutic longitudinal monitoring of Aβ aggregation in the brain. Therefore, estimation of the radiation dose exposure from each PET radioligand and the use of well-balanced PET scan protocols taking into consideration subject risk and benefit are important.
Estimation of the internal radiation dose requires a time series measurement of the biodistribution of the injected radioligand. There are two ways to establish the biodistribution of a radioligand in humans: one is to extrapolate from data obtained in animal experiments  and the other is to use data from a clinical whole-body PET study . Data extrapolated from animal experiments have been used to estimate clinical radiation dose. However, Sakata et al. reported that in some radioligands, there were considerable differences in organ dose or kinetics between human and animal experiments and that a whole-body PET study would be desirable for the initial clinical evaluation of new PET radioligands .
Previous biodistribution and dosimetry study for PET amyloid imaging
Recently, radiation dose exposures from several PET amyloid imaging agents have been reported using clinical whole-body PET scans. One of the popular amyloid ligands, Pittsburgh compound B ([11C]PIB), has been extensively investigated with regard to its kinetics in the human body, and its effective radiation dose was found to be 4.74 μSv/MBq on average . For 18F-labelled PET amyloid radioligands, effective doses in humans have been reported as follows: 18F-AV-45, 13 and 19.3 μSv/MBq [8, 9]; 18F-GE067, 33.8 μSv/MBq ; and 18F-BAY94-9172, 14.7 μSv/MBq .
Aim of the present study
Fluorinated amyloid imaging compound ([18F]FACT) is an 18F-labelled amyloid imaging agent developed at Tohoku University . Kudo and colleagues at this university have previously developed a 11C amyloid imaging agent named [11C]BF-227 . [18F]FACT is derived from [11C]BF-227 by reducing its lipophilicity in order to reduce the nonspecific binding in the brain; AD patients showed significantly higher uptake of [18F]FACT in the neocortex region relative to controls . However, the biodistribution of [18F]FACT in humans has not yet been investigated.
In the present study, the radiation dosimetry and biodistribution of [18F]FACT was investigated in healthy elderly subjects who are the target group for PET amyloid imaging. In order to determine the discrepancy in the estimated radiation dose between human and animal experiments, biodistribution studies in mice involving [18F]FACT were also conducted.
Information regarding the human subjects
BMI (kg/m 2)
Surgical removal of gallbladder
Mean ± 1 SD
76.3 ± 3.2
1.58 ± 0.75
59.2 ± 11.6
23.5 ± 2.7
This study was approved by the Ethics Committee on Clinical Investigations of Tohoku University School of Medicine and was performed in accordance with the Declaration of Helsinki. Written informed consent was obtained from all subjects after a complete description of the study had been made.
Radiochemistry and radioligand purity
All whole-body PET studies were performed using a SET-2400W scanner (Shimadzu Inc., Kyoto, Japan) in two-dimensional (2D) mode . The PET scanner acquired 63 image slices at a centre-to-centre interval of 3.125 mm and had a spatial resolution of 3.9 mm full width at half maximum (FWHM) and a Z-axis resolution of 6.5 mm FWHM at centre field of view .
Urination was controlled before, after and during the series of PET studies. In particular, during (15 min after the end of the first emission scan) and after the PET scans, subjects were asked to void. The volume and radioactivity levels of their urine samples were measured using a calibrated well counter.
All subjects underwent T1-weighted magnetic resonance imaging (MRI) scans using a Signa 1.5-T machine (General Electric Inc., Milwaukee, WI, USA) within a week of the PET scans. For each position (brain, chest, abdomen and epigastric region), individual T1-weighted scans with a voxel size of 1.875 × 1.875 × 6.000 mm (TR = 460 ms, TE = 14 ms, image matrix = 256 × 256 × 40) were obtained with subjects holding their breath.
where D i is the absorbed dose of the i th target organ, w i is the weighting risk factor in the i th target organ, and Q is the quality factor (Q = 1 for β- and γ-rays).
Regions of interest
[ 18 F]FACT time-integrated activity coefficients in the source organs
Mean ± 1 SD
5.38E−04 ± 2.98E−04
4.20E−02 ± 8.44E−03
8.40E−03 ± 4.37E−03
2.22E−01 ± 1.05E−01
Lower large intestine content
2.12E−02 ± 2.03E−02
Small intestine content
8.78E−02 ± 1.08E−01
6.71E−03 ± 2.28E−03
Upper large intestine content
2.55E−02 ± 1.89E−02
1.12.E−02 ± 1.51E−03
7.50E−03 ± 1.84E−03
1.34E−02 ± 3.27E−03
4.92E−01 ± 1.05E−01
3.55E−02 ± 1.16E−02
4.66E−01 ± 3.73E−01
5.53E−04 ± 3.79E−05
4.13E−03 ± 9.75E−04
3.98E−02 ± 4.33E−03
5.41E−03 ± 1.74E−03
5.77E−04 ± 4.67E−04
3.53E−04 ± 1.55E−04
Urinary bladder contents
2.26E−02 ± 8.36E−03
4.46E−03 ± 1.90E−03
Remainder of the body
1.17 ± 3.63E−01
For visceral organs with extremely high uptake (liver and gallbladder), individual ROIs were defined at a fixed emission scan with about a 40% threshold against the maximum counts (first emission for the liver and third or fourth emission for the gallbladder). Then the ROI was applied to the other emission images with minor adjustment of its location or shape. For the intestines, if specific high uptake was observed, individual ROIs were defined on each time frame of the PET images with about a 10% threshold. If there was no specific high uptake in the intestines, and uptake could be regarded as uniform, individual ROIs were drawn around the corresponding area.
In order to obtain a typical radioactivity concentration within organs with less location mismatch between PET and the co-registered MRI images (brain, breast, heart wall, heart contents, kidney, liver, lung, muscle, bones, spleen and thyroid), individual ROIs were drawn on co-registered MRI images. For other low-uptake organs (adrenal gland, stomach contents, pancreas, ovary, uterus and testis), individual ROIs were drawn on each time frame of the PET images and referred to the co-registered MRI images. To avoid a partial volume effect, the size of the ROI for these MRI available organs was made slightly smaller than the entire source organ. It should also be noted that all activities in vertebrae ROIs was assumed to be in the red marrow in the present study.
where V (ml) is the organ volume, and V reference is V of the reference subject (we used a 70-kg adult male and 58-kg adult female as the male and female reference subjects) [16, 17]. Even though some organs such as the intestine may change their volume over time, we used the reference subjects' organ volumes over the time period of the calculation of the %ID.
The time-integrated activity coefficient τ (Bq-h/Bq) in Equation 1 was obtained by fitting (%ID(t)) using a mono-exponential function and integrating from time zero to infinity. If the time-activity curve did not converge at the last PET scan (e.g. intestines and gallbladder), time-activity curves were fitted using two exponential functions, and then the area under the curve after the acquisition of the last image was calculated by assuming only physical decay of 18F and no additional biologic clearance to be conservative . The time-integrated activity coefficient for urinary bladder content was calculated by applying the dynamic urinary bladder model  to the urine samples with a bladder voiding interval of 2 h. The decay-corrected cumulative activity for urine was fitted using the equation A × (1 − exp(−ln(2) × t / τ)), where τ is the biological decay and A is the fraction of activity released from the body. The sum of the time-integrated activity coefficient for the specific organs was subtracted from the time-integrated activity coefficient for the total body, which was calculated from the time integral of the decaying injected radioactivity. Then the residual of the subtraction was regarded as the time-integrated activity coefficient in the remainder of the body. All fitting procedures were undertaken using a mean fit of R2 of 0.93 ± 0.13.
Finally, the time-integrated activity coefficient τ (Bq-h/Bq) was used to calculate the absorbed dose, D, in Equation 1 and the effective dose, E, in Equation 2. Both kinetics calculations (fitting and integration) and dose estimation were performed using OLINDA/EXM software version 1.0 (Department of Radiology and Radiological Sciences Vanderbilt University, Nashville, TN, USA) .
where the bodyweight of the mouse was assumed to be 30 for [18F]FACT.
Finally, in the same manner as in the human PET data analysis, time-integrated activity coefficients, absorbed doses and effective doses were calculated using the OLINDA/EXM software version 1.0. Sampled blood, thighbone and urine were regarded as heart contents, red bone marrow and urinary bladder contents, respectively.
Biodistribution of [18F]FACT
Estimated dose of [18F]FACT
Absorbed doses in the source organs
All subjects (n= 6)
1.96E01 ± 2.00
9.91 ± 1.82
8.69 ± 2.55
3.33E02 ± 2.51E02
Lower large intestine wall
2.52E01 ± 1.26E01
3.36E01 ± 3.07E01
1.61E01 ± 3.44
Upper large intestine wall
2.98E01 ± 1.50E01
1.62E01 ± 1.70
2.01E01 ± 4.30
7.75E01 ± 1.45E01
1.46E01 ± 1.10
1.03E01 ± 1.27
1.67E01 ± 6.65
2.32E01 ± 3.11
1.31E01 ± 1.70
1.60E01 ± 3.65
7.30 ± 1.39
1.37E01 ± 2.48
7.32 ± 2.16
1.00E01 ± 1.85
8.36 ± 1.38
Urinary bladder wall
2.23E01 ± 7.33
1.67E01 ± 8.13
1.38E01 ± 1.63
Effective dose (μSv/MBq)
1.86E01 ± 3.74
High absorbed dose in humans was observed in the gallbladder (333 ± 251 μGy/MBq), liver (77.5 ± 14.5 μGy/MBq), small intestine (33.6 ± 30.7 μGy/MBq), upper large intestine (29.8 ± 15.0 μGy/MBq) and lower large intestine (25.2 ± 12.6 μGy/MBq). In mice, high absorbed doses were observed in the small intestine (38.5 μGy/MBq), liver (25.5 μGy/MBq) and urinary bladder wall (43.1 μGy/MBq) for [18F]FACT (Table 3).
The effective dose estimated from the human PET study was 18.6 ± 3.74 μSv/MBq. The effective doses of [18F]FACT estimated from the clinical PET studies among other 18F-labelled PET amyloid radioligands were as follows: [18F]AV-45, 13 and 19.3 μSv/MBq [8, 9]; [18F]GE067, 33.8 μSv/MBq ; and [18F]BAY94-9172, 14.67 μSv/MBq . For PET analysis of [11C]PIB, Scheinin et al. normalised the %ID using the ratio of individual and reference subjects' body weights (Equation 4) . However, in the present study, we did not normalise the %ID data because there was a small difference between the effective dose with normalisation (17.6 ± 2.12 μSv/MBq) and the present effective dose (18.6 ± 3.74 μSv/MBq). Therefore, we concluded that body weight normalisation does not influence the effective dose.
The effective dose of [18F]FACT from the mouse experiments (14.8 μSv/MBq) was underestimated as compared with that from the human subject PET studies (18.6 μSv/MBq) (Table 3). This discrepancy corresponded to 0.76 mSv (2.96 and 3.72 mSv from mice and humans, respectively) while assuming an injected activity of 200 MBq as a clinically relevant dose. The underestimation of absorbed dose in the mouse gallbladder (20 times lower) and liver (3 times lower) relative to the human PET studies may have been responsible for the underestimation of the effective dose. High absorbed doses in the liver, gallbladder and small intestine of mice indicated that the biodistribution pattern of [18F]FACT in mice includes hepatobiliary excretion, as was observed in the PET scans involving human subjects. However, the estimated absorbed dose in the gallbladder was 20 times lower than the estimate from human subject data sets because we could not remove the gallbladder of the mouse. Therefore, to evaluate the effective dose of [18F]FACT in target organs, a whole-body PET scan of human subjects may be preferable as compared with the extrapolation from mouse experiments.
Clinical applicability of [18F]FACT
The present whole-body PET study was performed using healthy elderly subjects and not patients with AD. Previously, Koole et al. speculated that if brain uptake of 18F amyloid ligand increased by a factor of three, this will only influence estimation of the effective dose within 1%; however, when the subject had taken medication that changed the function of the hepatic metabolism, the estimated effective dose will vary with a larger range .
In the present series of PET studies, brain PET scans using the 3D mode were performed between the first and the second emission scan. Therefore, the injected dose for 2D whole-body scans was set to lower level than usual, and the averaged injected activity of 160.8 MBq corresponded to a radiation dose of 2.99 mSv per single administration. With regard to the optimal injected activity that can ensure sufficient image quality for clinical use, the peak noise-equivalent counts ratio (NECR) is often used in its determination. It has also been reported that the peak NECR in 2D mode was not reached with an acceptable range of injected activity, whereas in 3D mode, there was a distinct maximum for the NECR for which the corresponding injected activity was based on patient height and weight . For the scanner used in our study, the NECR peak in 3D mode was reached at 4.44 kBq/ml using an 8,000-ml phantom . When the subject's height and weight were assumed to be 170 cm and 60 kg, respectively, this assumption corresponded to the optimal injected dose of about 260 MBq. In a real situation, there exists the effect of the activity outside the axial FOV, and the optimal injected dose would be much lower. Injected activity indicates radiation dose; for example, 200 MBq indicates a radiation dose of 3.72 mSv. ICRP 62  recommended that the maximum radiation dose that causes a ‘minor to intermediate’ increase of risk levels while preserving social benefit levels that are ‘intermediate to moderate’ has an effective limit of 10 mSv/year [20, 21]. Thus, the maximum injectable activity is 537.6 MBq [18F]FACT/year, and this injection dose limit allows two or three PET scans to be performed. Furthermore, amyloid imaging is mainly undertaken in elderly patients aged >50 years, even though for early detection of AD, patients aged <50 years will also have an amyloid PET scan. According to the guidance on medical exposures in medical and biomedical research by the European Commission , dose restrictions for patients aged over >50 years are not as strict as for younger patients. Therefore, considerably more multiple PET scans may be possible.
The effective dose of the 18F-labelled amyloid imaging agent, [18F]FACT, was found to be acceptable for clinical study.
We would like to thank Dr. Muneyuki Sakata from the Positron Medical Center, Tokyo Metropolitan Institute of Gerontology, and Dr. Hiroshi Watabe from the Cyclotron Radioisotope Center, Tohoku University, for their helpful advice regarding data analysis. This study was supported in part by Grants-in-Aid of Young Scientists (B) (no. 24700445) from the Ministry of Education, Culture, Sports, Science and Technology (MEXT), Japanese Government.
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