Positron emission tomography (PET) has been widely used for clinical and preclinical studies, including disease diagnosis, treatment monitoring, and drug development. Compared to other imaging modalities, such as magnetic resonance imaging (MRI), ultrasound, and optical imaging, PET is highly sensitive and quantitative1. However, the high cost of PET imaging has been the key roadblock for its widespread routine use. The high cost originates from expensive radionuclide production and tracer preparation, which must be conducted on-site1. Here, we demonstrated the feasibility of a synthesis-free PET imaging method for brown adipose tissue (BAT). With this method, the cost of PET imaging could be dramatically reduced, thus allowing for a widespread application of this technology.

For the purpose of synthesis-free PET imaging, we considered the following criteria: 1) the radionuclide should have a suitable lifetime for delivery and transportation; 2) synthetic components (excluding the radionuclide) should be available in a convenient kit; and 3) the generation of the actual tracers should be very fast or the actual tracers should be formed in vivo. To meet the above requirements, we selected 64Cu as the radionuclide due to its reasonable decay lifetime (12.7 hours) and widespread availability. For our proof-of-principle studies we selected BAT as the biological target, because BAT has the following unique features making it a suitable imaging model2, 3: 1) BAT in mice is situated away from large organs such as liver, heart, and stomach, and thus signal interference from these large organs is minimal; 2) BAT is a whole mass organ; 3) BAT has a unique triangular physical shape which is easy to distinguish from other tissues.

In the past years, the clinical significance of BAT has been validated through a large-scale analysis of [18F]-FDG PET-CT images and other important studies4,5,6,7,8. BAT is a specialized tissue for thermogenesis in mammals, whose function is to dissipate large amounts of chemical/food energy as heat, thus maintaining the energy balance of the whole body9,10,11. In spite of the fact that investigations of BAT have been ongoing for 70 years, it had been assumed that BAT disappears from the body of adults and has no significant physiological relevance in adult humans9, 12,13,14. This “non-existence” assumption is partially due to the lack of proper imaging methods to “see” the small BAT depots in vivo, as only 3%-8% of BAT depots in adults could be clearly visualized with [18F]-FDG (the most used imaging method) if no cold or drug stimulation is applied6, 15,16,17. However, under stimulated conditions, [18F]-FDG PET imaging has shown that BAT is still present in 95% of healthy adults in the upper chest, neck, and other locations4,5,6. This remarkably large difference between non-stimulated and stimulated conditions strongly indicates that [18F]-FDG PET imaging primarily reflects the activation of BAT, but not BAT mass. Various other imaging methods for BAT are available for preclinical and clinical studies, however most of them are dependent on BAT activation18,19,20,21,22,23,24,25,26,27. Therefore, an imaging probe that can consistently report on BAT mass is highly desirable.

In this report, we first conducted a top-down screening, and found that the combination of 64CuCl2 and disulfiram (termed 64Cu-Dis) provided high contrast for BAT, which was not affected by BAT activation. We also found that TSPO, a transport protein located on the outer mitochondrial membrane28, was the binding target of 64Cu-Dis. We further validated that TSPO is an excellent but unexpected imaging biomarker for BAT using western blot, histology, and PET imaging with TSPO-specific ligand [18F]-F-DPA.


Screening for BAT-binding ligands

In our previous report3, we have demonstrated that a top-down screening approach could be used for seeking near infrared fluorescence (NIRF) imaging probes for BAT. In that study, we screened 38 NIRF dyes resulting in two hits that we further optimized for high BAT selectivity3. In this report, we used a similar top-down strategy for fast screening of a library of copper ligands, which could be used for fast coordination chemistry with no need for purification. Among the 16 screened ligands, four compounds were considered as positive hits (SI Fig. 1), including disulfiram, diethyldithiocarbamate (DDC, a metabolic product of disulfiram in vivo 29), cysteamine, and salicylaldoxime.

Using the combination of 64CuCl2 and disulfiram (64Cu-Dis) for “synthesis-free” PET imaging

One of the lead ligands, disulfiram, caught our attention, because it is an FDA approved drug for alcoholism30. Disulfiram, a disulfide compound, does not have a strong affinity to copper. However, when injected in vivo, it is reduced to the monomer and releases the thiol group producing diethyldithiocarbamate (DDC), which has a high affinity for copper (II) (Fig. 1a)29, 31. Considering that DDC, a metabolic product of disulfiram, is an active copper chelator, we proposed a step-wise injection strategy to realize synthesis-free PET imaging (Fig. 1b). To this end, we injected disulfiram intraperitoneally (40 mg/kg) in mice and allowed 60 minutes for it to metabolize into DDC, the active copper binding form. It has been reported that disulfiram can be rapidly and quantitatively reduced to DDC within 4 minutes and the half-life of DDC in human and dog blood was 70- and 100-minutes32. Considering the above facts, we chose 60-minutes as the interval time between injections of disulfiram and 64CuCl2. Next, we intravenously injected 64CuCl2, which can quickly chelate with DDC in vivo. Strikingly, we found that BAT could be easily identified by PET imaging as early as 10 minutes (Fig. 1c), and as late as 48 hours after injections. The uptake of the tracer at 30 minutes after 64CuCl2 injection was 10.6% ID/g (Fig. 1d). More importantly, no apparent signal could be observed from WAT (white adipose tissue), including inguinal and epidermal areas (Fig. 1d and SI Fig. 2a,b), indicating that this method has high BAT selectivity over WAT.

Figure 1
figure 1

(a) In-vivo chemistry of Disulfiram, an inactive copper ligand. It metabolizes to DDC, an active copper ligand, to form the active PET tracer with 64CuCl2 in vivo. (b) Diagram of synthesis-free PET imaging via stepwise injection of Disulfiram and 64CuCl2 (64Cu-Dis) 30 minutes after 64CuCl2 injection. (c) Representative PET images of a mouse injected consecutively with Disulfiram and 64CuCl2 (64Cu-Dis) 30 minutes after 64CuCl2 injection. Coronal view (left), sagittal view (right), and transverse view (upper corner). The triangular shape of BAT can be easily identified. (d) Quantitative analysis of the tracer uptake from in vivo imaging with 64Cu-Dis in interscapular BAT (iBAT), gonadal WAT (gWAT) and inguinal WAT (ingWAT). (e) Ex vivo bio-distribution of the tracer in iBAT, interscapular WAT (iWAT), gWAT and ingWAT.

Attaining high BAT/WAT selectivity has been one of the challenges for developing imaging probes for BAT. To confirm the data on BAT/WAT selectivity obtained from in vivo PET imaging, we conducted ex vivo bio-distribution of BAT and WAT tissues 6 hours after 64CuCl2 injection. We found that interscapular BAT uptake was 13.1% ID/g, which was 10-fold higher than that of interscapular WAT, inguinal WAT, or gonadal WAT (Fig. 1e). Taken together, our in vivo imaging data were consistent with the ex vivo data, suggesting that 64Cu-Dis was highly selective for BAT over WAT. Full ex vivo bio-distribution data could be found in SI Fig. 2c.

We also conducted control experiments with 64CuCl2 only, and found that BAT uptake was about 2.47% ID/g (SI Fig. 3a), which was much lower than that with 64Cu-Dis (10.6% ID/g), suggesting that disulfiram is necessary for high BAT uptake. Interestingly, we also noticed that the pharmacokinetics of 64Cu-Dis and 64CuCl2 only were apparently different (SI Fig. 3b and c). There was no apparent clearance from liver, kidney, and bladder after 64CuCl2 injection within 24 hours, while noticeable clearances from these organs could be observed with 64Cu-Dis. Meanwhile, the time courses of BAT uptake with 64Cu-Dis and 64CuCl2 only were also evidently different, and clear washing-out could be seen with 64Cu-Dis. These differences were likely due to the fact that disulfiram can be rapidly metabolized to its monomer DDC to instantly form Cu(DDC)2 complex in vivo 29, 31. Taken together, our data suggested that the contribution to BAT uptake from free 64CuCl2 was not significant when our step-wise injection protocol of 64Cu-Dis was used for BAT imaging.

In vivo BAT imaging with 64Cu-Dis

To investigate whether the “synthesis-free” method can be used to consistently image BAT mass under different conditions, we imaged mice under a normal condition and under cold exposure, which is a standard protocol for BAT activation2, 33. For cold exposure, the mice were placed in a cold room at 4 °C for 2 hours before and 1 hour after disulfiram administration. Next, the mice were injected with 64CuCl2 and kept at 4 °C for 30 minutes followed by imaging for 30 minutes (Fig. 2a). BAT uptake was about 10.0% ID/g for normal conditions at 1 hour after 64CuCl2 injection with no significant decrease at 6 hours (SI Fig. 4). Importantly, we found that there was no significant difference in uptake between normal and cold treated groups (Fig. 2b,c). This is contrary to [18F]-FDG PET and other imaging methods, in which BAT contrast is highly dependent on its activation status. Our data suggested that this synthesis-free method could be used for reporting BAT mass regardless of BAT activation status.

Figure 2
figure 2

PET images of mice injected 64Cu-Dis under normal and cold exposure conditions. (a) Representative coronal image under a normal condition, (b) Representative coronal image under a cold exposure condition, and (c) Quantitative analysis of (a) and (b). There was no significant difference in uptake between control and cold treated groups (p = 0.359).

Blocking studies with TSPO-specific ligand F-DPA

Our in vivo and ex vivo results revealed that the 64Cu-Dis combination was indeed a synthesis-free method for PET imaging of BAT, however, it was not clear what the molecular binding target was. By surveying the publications reporting on the disulfiram mechanism of action, and found that TSPO could be a target candidate34, 35. To investigate whether the uptake of disulfiram or DDC is related to TSPO, we conducted blocking studies using the TSPO specific ligand F-DPA (Ki = 9 nM) (Compound 3 K in ref. 36, and structure in SI Fig. 5c)36. F-DPA is an analogue of [18F]-DPA-71437, and is a highly selective ligand for TSPO36, 38. In these experiments, we intravenously injected 3.0 mg/kg of F-DPA after ip injection of disulfiram, and imaged the mice using the same protocol as above. Images were captured at 1 hour and 6 hours after 64CuCl2 injection. Indeed, we found that F-DPA could effectively block BAT signal at both time points (Fig. 3a,b), with a 35.0% and 60.0% decrease respectively (Fig. 3c,d). Interestingly, we also observed a significant decrease in PET signal from other organs such as heart and kidney (Fig. 3e,f and SI Fig. 5a,b), in which TSPO has reportedly high expression39. Therefore, our data strongly suggested that high BAT contrast was associated with TSPO.

Figure 3
figure 3

Blocking studies with TSPO ligand F-DPA. (a) Representative PET images of mice injected with 64Cu-Dis without blocking. (b) Representative PET images of mice with 64Cu-Dis with F-DPA blocking. The decreased uptake of 64Cu-Dis can be observed in BAT (white arrow) and heart (arrow head). (c) Quantitative analysis of BAT uptake at 1 hour, (d) Quantitative analysis of BAT uptake at 6 hours, (e) Quantitative analysis of kidney uptake at 6 hours, and (f) quantitative analysis of heart uptake at 6 hours. *Indicates p < 0.05.

Biological validation of TSPO as a specific biomarker for BAT imaging

To further confirm that TSPO can be used as a specific imaging biomarker for BAT, we performed biological analyses. TSPO, also called translocator protein or peripheral benzodiazepine receptor (PBR)28, 39, is located on the outer mitochondrial membrane. It is well known that one of its characteristic features of BAT is its high abundance of mitochondria compared to WAT9,10,11. It is likely that the abundance of TSPO in BAT is much higher than that in WAT. Nonetheless, no experimental data are available indicating whether TSPO expression in BAT and WAT is significantly different, which is crucial for determining whether TSPO can be used as a specific imaging biomarker for BAT. To answer this question, we compared the qPCR data of TSPO in BAT and WAT, and found that the mRNA level in BAT was about 1.5-fold higher than in WAT (SI Fig. 6). To further confirm different levels of TSPO protein expression in BAT and WAT, we performed western blot with anti-TSPO antibody. As shown in Fig. 4a, protein level in BAT was about 20-fold higher than in WAT (Fig. 4a,b, the full length of the blot could be found in SI Fig. 6b). We next investigated the abundance of mitochondria in BAT and WAT tissues using a mitochondria specific dye (MitoTrack deep red FM). As expected, BAT showed much higher fluorescence intensity than WAT (Fig. 4c). In addition, we performed immunological staining of BAT and WAT tissues with anti-TSPO antibody. Figure 4d demonstrated that the abundance of TSPO in BAT was significantly higher than that in WAT. In conclusion, our data for the first time suggested that TSPO could be used as a specific imaging biomarker for BAT.

Figure 4
figure 4

Biological validation of high expression level of TSPO in BAT. (a) Western blot of BAT and WAT tissue extractions with anti-TSPO antibody (lane1–4: four duplicated BAT samples; lane5–8: four duplicated WAT samples), and the full length of blot could be found in SI Fig. 6b, (b) quantification of (a). Note higher TSPO level in BAT compared to WAT. (c) Histological staining of BAT (left) and WAT (right) tissue slices with mitochondria specific dye MitoTrack deep Red, and (d) immunohistological staining of BAT and WAT tissue with anti-TSPO antibody (green) and DAPI for nuclei (blue). Scale bar: 30 μm.

PET imaging of BAT with TSPO-specific tracer [18F]-F-DPA

To further validate whether TSPO is a specific imaging biomarker for BAT, we investigated whether existing TSPO-specific PET tracers could provide high contrast for BAT over WAT. To this end, we used18F-labeled TSPO-specific ligand [18F]-F-DPA36,37,38, 40. We first performed PET imaging in Balb/c mice using a 20-minutes static scan. As seen in Fig. 5a–c, there was a readily identifiable contrast from BAT with a 16% ID/g uptake at 30 minutes after the injection. Moreover, we also compared images at locations with high WAT abundance and found that inguinal and gonadal WAT had minimal uptake (SI Fig. 7).

Figure 5
figure 5

Representative PET images of mice injected with [18F]-F-DPA. (a) Coronal view, (b) sagittal view, and (c) transverse view. The triangular shape of BAT can be clearly identified. (d) Quantitative analysis of BAT uptake under normal and cold exposure. There was no significant difference between these two groups (p = 0.356).

To further validate the uptake of [18F]-F-DPA in BAT, we conducted a bio-distribution study in Balb/c mice at 45 minutes after the probe injection. BAT, inguinal WAT and gonadal WAT, brain, liver, and heart were harvested (SI Fig. 8). The bio-distribution data confirmed a higher uptake of the tracer in BAT compared to other organs, suggesting that [18F]-F-DPA was highly selective for BAT compared to WAT. Taken together, the high uptake in BAT with established TSPO PET ligand supports our hypothesis that TSPO could serve as an imaging biomarker for BAT.

[18F]-F-DPA uptake is not influenced by BAT activation

To investigate whether [18F]-F-DPA can be a reliable PET tracer for BAT mass, we conducted PET imaging under BAT activation with cold exposure. Mice were exposed to 4 °C for 2 hours before imaging. Our imaging data showed that there were no significant differences between cold treatment and normal condition, indicating that [18F]-F-DPA could serve as a reliable tracer for BAT mass independent of its activation (Fig. 5d). Thompson et al. have recently showed that TPSO expression could not be altered by acute cold exposure, which is consistent with the data obtained in our experiment41. This also suggests that TSPO is a reliable biomarker for BAT mass.

Discussions and Conclusions

PET imaging is immensely useful for both clinical and preclinical applications, however its high cost prevents it from being widely applicable. Requirements for an on-site cyclotron and on-site synthesis are among the major contributors of the high cost. In this report, we demonstrated the feasibility of a synthesis-free PET imaging. Although we demonstrated the application of this method for a specific case that involved imaging of BAT mass, we believe that “pseudo-synthesis-free” and “synthesis-free” methods could be used for other applications as well. “Pseudo-synthesis-free” methods can be realized with fast and strong chelation reaction of ligands with suitable radionuclides. “Synthesis-free” could be feasible if some compounds, which have strong coordination with the radionuclides, could pre-target receptors/enzymes, or if peptides/proteins that have strong chelation with radionuclides could be engineered into specific targets.

In the present study, disulfiram was used as a precursor of a copper ligand, and the actual PET tracer formed in vivo via the chelation of 64CuCl2 with DDC, the in vivo metabolite of disulfiram. In 2014, Nomura et al. reported that disulfiram could serve as an efficient copper delivery drug to the brain in Menkes disease, which is characterized by dysfunction in copper transporting42. Brain images from our study (Fig. 1) showed a significant amount of copper accumulated in the brain, which is consistent with the reported results42.

Recent large clinical data have clearly demonstrated that BAT is tightly linked to obesity and diabetes4,5,6,7,8. However, imaging methods that can reliably reflect BAT mass are still in shortage. Our data suggested that both 64Cu-Dis and [18F]-F-DPA could be used to reliably report on BAT mass, regardless of the activation status of BAT. This is very different from most used BAT tracers such as [18F]-FDG and others, including MRI and optical imaging probes. Interestingly, compared to [18F]-FDG imaging, the images obtained with our method more reliably contour the unique triangle shape of BAT.

Our studies indicate that the BAT contrast is due to the binding of 64Cu-Dis to TSPO, which is consistent with previous reports34, 35. Katz and Gavish reported that disulfiram and DDC were competitive inhibitors for TSPO or PBR (peripheral benzodianzepine receptor)34. They demonstrated that disulfiram and DDC could effectively replace binding of classical TSPO ligands such as Ro5-4864. Gilman et al. showed by PET imaging that disulfiram could reduce the uptake of TSPO ligand11C-Flumazenil in human brain35. In spite of the fact that TSPO has been an imaging target for a long time, particularly for brain imaging, very few reports have emerged utilizing it for peripheral target imaging, and biological evaluation of the high TSPO expression level in BAT is rare41. In the present study, for the first time, we validated TSPO as an imaging biomarker for BAT.

“Browning”, a process of turning WAT into BAT43,44,45 represents an exciting approach for converting “bad fat” to “good fat” (BAT and beige fat). Since the “browning” process could result in more mitochondria, and our method is capable of detecting the abundance of TSPO in mitochondria, it is reasonable to speculate that our methods have the potential to monitor the browning process, in which the abundance of TSPO increases with the increase of BAT-like cells.

Although TSPO was discovered nearly 40 years ago, its functions in obesity and adipocytes are not well explored. Our studies discovered and confirmed high TSPO expression in BAT, which opened a new avenue for basic BAT research aimed at investigation of biological functions of TSPO. In addition, since TSPO is tightly associated with inflammation28, it is conceivable that 64Cu-Dis is also suitable for imaging inflammation in different diseases.

In summary, we demonstrated that a synthesis-free method for PET imaging was feasible, and the combination of 64CuCl2 and disulfiram could be used for BAT imaging. We also validated, for the first time, TSPO as an imaging biomarker for BAT. We believe that our method can be widely applied for TSPO and BAT imaging, and that the synthesis-free strategy could significantly reduce the cost of PET imaging.

Materials and Methods

All of the chemicals were purchased from commercial vendors and used without further purification. Disulfiram was purchased from USP (Cat. No. 1224008, Rockville, MD), and dissolved in a solution of 15% DMSO and 85% Cremophor EL (10 mg/ml). F-DPA and [18F]-F-DPA were synthesized in Dr. Steven H. Liang laboratory (Massachusetts General Hospital). Balb/c mice and B6C3F1/J mice were purchased from Jackson Laboratory. All animal experiments were approved by the Institutional Animal Use and Care Committee (IACUC) at Massachusetts General Hospital, and carried out in accordance with the approved guidelines.

MicroPET imaging of mice with 64Cu-Dis

In vivo PET imaging was conducted with 7-month old B6C3F1/J mice. Mice were anesthetized with isoflurane/oxygen for 5 minutes, and then injected intraperitoneally (i.p.) with 100 μL (40 mg/kg) solution of disulfiram (10 mg/ml). After 60 minutes, mice were injected intravenously (i.v.) with 100 μL 64CuCl2 (100–150 μCi) solution in PBS, pH 7.4. After 0.5- and 6-hours, PET imaging was conducted using a 30-minutes static imaging on a Sophie Biosciences microPET G4 scanner (Culver City, CA, USA). Imaging analysis was conducted using Amide, a Medical Imaging Data Examiner.

Cold exposure treatment

Mice (B6C3F1/J) were placed into cold room (4 °C) for 2 hours, and then i.p. injected with 100 μL (40 mg/kg) solution of disulfiram (10 mg/ml). The injected mice were then returned to the cold room for 1 hour, and then i.v. injected with 100 μL 64CuCl2 (100–150 μCi) in PBS, pH 7.4. After 30 minutes in the cold room, mice were imaged using a 30-minutes static imaging on the G4 scanner.

Ex vivo bio-distribution of 64Cu-Dis

Four-month old Balb/c mice were anesthetized with isoflurane/oxygen for 5 minutes, and then i.p. injected with 100 μL (40 mg/kg) solution of disulfiram (10 mg/ml). After 60 minutes, mice were i.v. injected with 100 μL of 64CuCl2 (100–150 μCi) solution in PBS, pH 7.4. After six hours, mice were sacrificed, and interscapular BAT, interscapular WAT, inguinal WAT, gondal WAT and other organs were excised and subjected to counting in a scintillation counter (Packard Cobra II Auto Gamma Scintillation Well Counter).

Blocking studies with TSPO ligand F-DPA

Mice (B6C3F1/J) were i.v. injected with 100 μL solution (3 mg/kg) of F-DPA in 15% DMSO, 15% Cremophor EL and 70% PBS, and then i.p. injected with 100 μL (40 mg/kg) solution of disulfiram. The injected mice were returned to the cage for 1 hour, and then i.v. injected with 100 μL of 64CuCl2 (100–150 μCi) in PBS. After 0.5- and 6-hours, mice were imaged using a 30-minute static imaging on the G4 scanner.

Semi-Quantitative PCR Analysis

Total RNA was extracted from the adipose tissue using TRIzol (Invitrogen, Grand Island, NY). The cDNA was synthesized by iScriptTM system (Bio-Rad, Hercules, CA). Reverse transcription reaction was performed using a PTC-100 programmable thermal controller (MJ Research Inc., Waltham, MA). A real time PCR was performed using an iTaqTM universal STBR® green Supermix (Bio-Rad, Hercules, CA) in an Mx3005 P qPCR thermocycler (Agilent Technologies, Santa Clara, CA). All values were normalized to cyclophilin expression and further analyzed using the ΔΔC T method. The sequences of primers used in the semi-quantitative PCR were as following: TSPO (forward: 5′-CCATGGGGTATGGCTCCTACA-3′, reverse: 5′-CCAAGGGAACCATAGCGTCC-3′); cyclophilin (forward: 5′-GGAGATGGCACAGGAGGAA-3′, reverse: 5′-GCCCGTAGTGCTTCAGCTT-3′).

Western blotting with anti-TSPO antibody

Adipose tissue was homogenized in a RIPA lysis buffer (Millipore) supplemented with protease and phosphatase inhibitor cocktails (Thermo Scientific). Homogenates were centrifuged at 13,000 r.p.m. at 4 °C for 20 minutes, and the supernatants were used as tissue lysates. Protein concentration was determined by BCA protein assay. Seventy micrograms of protein lysate was separated in a 4–20% SDS–PAGE gel. The separated proteins were transferred to a polyvinylidene difluoride (PVDF) membrane, which was then blocked in 5% NFDM at room temperature for 2 hours. After blocking, the membrane was incubated with anti-TSPO primary antibody in TBST buffer (1:1000 dilution, Cell Signaling) at 4 °C overnight. After washing with TBST buffer, the membrane was incubated with the secondary antibody (goat anti-rabbit IgG (H + L), Invitrogen) for 1 hour at room temperature. Western Pico Chemiluminescent Substrate (Thermo scientific) was used to visualize the bands. The images were acquired with IVIS®Spectrum (Perkin Elmer, Hopkinton MA) using bioluminescence imaging setting. PageRular Plus Prestained Protein Ladder (Thermo Fisher) (10–250 KD) was used as a molecular weight marker.

Immunohistochemistry with anti-TSPO antibody and histochemical staining with MitoTracker

Adipose tissue was fixed in 4% formaldehyde at room temperature for 24 hours, embedded in paraffin and cut into 5-micron slices. For immunostaining, heat mediated antigen retrieval was first performed using Antigen Retrieval Citra Plus Solution (Biogenex), and then the sections were blocked with 5% NFDM for 1 hour at room temperature. After that, the samples were incubated with anti-PBR/TSPO antibody (Abcam, ab109497) diluted in a blocking buffer overnight at 4 °C. After washing with TBST, the samples were incubated with secondary FITC-labeled antibody for 1 hour at room temperature and counterstained with DAPI. For Mitochondria staining, deparaffinized sections were incubated with MitoTracker probes (500 nM) (Invitrogen, MitoTracker® Deep Red FM, cat. No. M22426) for 30 minutes at room temperature. Images were captured using a Nikon ECLIPSE 50i fluorescence microscope.

In vivo PET imaging with [18F]-F-DPA

In vivo PET imaging was conducted with C57BL/6 J mice. For cold treatment, mice were placed in the cooled room (4 °C) for 2 hours. Mice were i.v. injected with 100 μL of 20–30 μCi [18F]-F-DPA in 10% ethanol saline. PET imaging was conducted using a 20-minutes static scan on a Sofie Biosciences microPET G4 scanner under short anesthesia (isoflurane/O2) (2–3 minutes). Imaging analysis was conducted with Amide.