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In Vivo Optical Imaging of Interscapular Brown Adipose Tissue with 18F-FDG via Cerenkov Luminescence Imaging

Objective Brown adipose tissue (BAT), a specialized tissue for thermogenesis, plays important roles for metabolism and energy expenditure. Recent studies validated BAT’s presence in human adults, making it an important re-emerging target for various pathologies. During this validation, PET images with 18F-FDG showed significant uptake of 18F-FDG by BAT under certain conditions. Here, we demonstrated that Cerenkov luminescence imaging (CLI) using 18F-FDG could be utilized for in vivo optical imaging of BAT in mice. Methods Mice were injected with 18F-FDG and imaged 60 minutes later with open filter and 2 minute acquisition. In vivo activation of BAT was performed by norepinephrine and cold treatment under isoflurane or ketamine anesthesia. Spectral unmixing and 3D imaging reconstruction were conducted with multiple-filter CLI images. Results 1) It was feasible to use CLI with 18F-FDG to image interscapular BAT in mice, with the majority of the signal (>85%) at the interscapular site originating from BAT; 2) The method was reliable because excellent correlations between in vivo CLI, ex vivo CLI, and ex vivo radioactivity were observed; 3) CLI could be used for monitoring BAT activation under different conditions; 4) CLI signals from the group under short-term isoflurane anesthesia were significantly higher than that from the group under long-term anesthesia; 5) The CLI spectrum of 18F-FDG with a peak at 640 nm in BAT after spectral unmixing reflected the actual context of BAT; 6) Finally 3D reconstruction images showed excellent correlation between the source of the light signal and the location and physical shape of BAT. Conclusion CLI with 18F-FDG is a feasible and reliable method for imaging BAT in mice. Compared to PET imaging, CLI is significantly cheaper, faster for 2D planar imaging and easier to use. We believe that this method could be used as an important tool for researchers investigating BAT.


Introduction
Brown adipose tissue (BAT) is a specialized tissue for thermogenesis in mammals, and it has been considered as a furnace in the body for burning excess calories. The function of BAT in mammals is to dissipate large amounts of chemical/food energy as heat, thus maintaining the energy balance of the whole body [1,2,3]. Investigations of BAT have been ongoing for decades, particularly using animals. It has been considered that BAT disappears from the body of adults and has no significant physiological relevance in adult humans [1,4,5,6]. However, recent rediscovery of BAT in human adults by PET-CT scan has produced a new driving force for BAT studies [7,8,9,10,11,12,13,14]. Multiple studies have demonstrated that BAT mass levels inversely correlate with body-mass index (BMI), and that physical exercises could increase BAT mass, suggesting that BAT may play important roles in obesity and diabetes [7,8,15,16,17]. In addition, BAT has emerged as an important target for various other diseases such as neurodegenerative disease and cancer [5,9,10,11,12]. Clearly, the ability to image BAT noninvasively would aid in clinical staging of various diseases as well as in drug development processes.
Cerenkov luminescence imaging (CLI) is a newly emerged molecular imaging technology [18,19,20,21,22,23,24,25,26,27]. It utilizes luminescence generated from the b + and b 2 decay of radionuclides such as 18 F and 131 I in the medium. As a charged particle (such as b + and b 2 ) travels, it polarizes molecules in the medium [18,19,20]. When the polarized molecules relax back to equilibrium they emit electromagnetic waves. As the particle moves along its path, the waves destructively interfere with each other and no radiation is observed. However, if the particle velocity v is greater than the speed of light in the medium (c/n, where c is the speed of light, and n is the index of refraction), then a shockfront comprised from constructive interference is observed as Cerenkov radiation. The intensity of the emitted Cerenkov photons is proportional to the kinetic energy of the charged particle, in this case, the b +/2 ejected from the radionuclide [28]. As the condition that v.c/n in the medium, the energy threshold necessary for Cerenkov light production varies for different media, dependent on the index of refraction. [19,28]. In addition, the spectrum of the radiation-luminescence consists of continuous wavelengths throughout the ultraviolet (UV) and visible spectrum [18,19,20], with the intensity distribution inversely proportional to the square of the wavelength. It is conceivable that the light emitted from the radionuclide with a shorter wavelength could be used a replacement of ultraviolet (UV) light, while the longer wavelength light could be used for in vivo imaging due to its superior tissue penetration. We have previously demonstrated that the UV portion of Cerenkov luminescence could be utilized for in vivo photoactivation of caged luciferin [21], while Dothager and Liu utilized this approach for quantum dots excitation [23,29]. Others have reported that CLI could be a reliable tool for imaging tumors, assisting intraoperative surgical resection, endoscopic imaging, and for monitoring therapeutic effectiveness of anticancer drugs [18,30,31,32,33,34]. Several excellent reviews have summarized the advantages and disadvantages of this technology [26,35,36]. Recently, Spinelli and Ackerman also demonstrated that Cerenkov luminescence from alpha-emitter daughter products could be used for imaging [37,38]. In this report, we demonstrated that CLI could be used for BAT imaging. BAT is an ideal target for CLI due to the following reasons: 1) Location of BAT in mice is unique since it is situated away from large organs such as liver, heart, and stomach, and thus signal interference from these large organs is minimal (Fig. 1a); 2) BAT location is shallow, which allows for more photons to reach the detection camera; 3) BAT is a whole mass organ; 4) BAT has a unique triangular physical shape which is easy to distinguish from other tissues (Fig. 1a).
PET (positron emission tomography) imaging confirmed the significant uptake of 18 F-FDG in BAT under certain conditions in humans [7,8,10,13,39]. Previous animal studies also demonstrated that 18 F-FDG could be significantly taken up by BAT in mice [40,41]. In this report, we hypothesized that BAT could be optically imaged with 18 F-FDG utilizing Cerenkov luminescence imaging.
For small animal research, we believe that CLI imaging of BAT could be a useful complementary method for PET imaging with 18 F-FDG, particularly for laboratories without an accessible PET scanner. Additionally, CLI imaging with an optical imaging system is cheaper and therefore, more cost effective. For simple 2D planar imaging it could be faster than PET imaging, and could potentially be used for high throughput screening. Apart from the ability to image BAT, our study also serves as an additional validation of CLI as an emerging imaging modality.

CLI Feasibility for BAT Imaging
To test whether CLI with 18 F-FDG is capable of providing significant signal and contrast, 10.3 MBq of 18 F-FDG was intravenously injected into nude mice. For each time point, mice were anesthetized by isoflurane, and the CLI images were acquired within 3 minutes after induction of anesthesia using a whole-body optical imaging system. No stimulation for BAT activation was applied. We found that CLI signals from interscapular BAT (Fig. 1a) were remarkably bright at all time points (30, 60, 120 minutes), and the contrast between BAT and the adjacent reference area was apparent (Fig. 1b). Signal ratios of BAT and the reference area were 2.37-, 2.49-, and 2.53-fold respectively at 30, 60, and 120 minutes after injection. Interestingly, contours of BAT images closely resembled its physical appearance (interscapular BAT of rodents consists of two lobes that make a triangle contour) (Fig. 1a). These results suggested that CLI imaging of BAT with 18 F-FDG was feasible.

Validation of the CLI Signal from the Interscapular Area
To confirm whether the majority of the interscapular CLI signal was from BAT, we first conducted biodistribution studies with CLI signal and radioactivity countings from the dissected tissues. Both CLI and radioactivity countings indicated that the heart and BAT were the two primary tissues for 18 F-FDG uptake, with BAT displaying the highest uptake ( Fig. 2a,b, and Fig. S1). Because the heart is located more deeply than the interscapular BAT when images were taken from the dorsal side, we speculated that the majority of the CLI signal in the interscapular area originated from BAT. To further validate this speculation, we imaged mice before and after BAT removal, and compared the images. We found that the majority of the signal (.85%) at the interscapular site originated from BAT (Fig. 2c,d). The residual signal was located near the upper rim of BAT and was most likely from the remnants of BAT tissue and other surrounding tissues, such as blood vessels, muscles, and bones.

CLI Reliability Study
Since CLI imaging is still in the developmental stage, crossvalidation of in vivo CLI signals with ex vivo CLI signals, as well as with its actual radioactivity, was necessary. It is known that activation of BAT by cold exposure or drugs (such as norepinephrine) is often needed to obtain reliable PET images [8,10,39,40]. In our studies, we used similar methods to show the reliability of Cerenkov luminescence imaging. We used norepinephrine (NE) as a stimulator in these studies. Mice were stimulated with NE followed by in vivo CLI with 18 F-FDG. Immediately after imaging, mice were sacrificed and BATs were collected and subjected to ex vivo CLI imaging and radioactivity measurements with a dosimeter. As expected, in vivo images of the NE-treated group showed significantly brighter signals than that of the non-treated control group (p,0.005, Fig. 3a and Fig. S2a). Ex vivo CLI quantitation and dosimetry countings displayed significantly higher values for the NE-treated group than for controls as well (p,0.01, Fig. 3b-c, and Fig. S2b-c). To further validate whether in vivo CLI signals reliably reflected the amount of radioactivity caused by 18 F-FDG accumulation in BAT, linear regression fitting was used to evaluate a correlation between in vivo CLI, ex vivo CLI, and ex vivo dosimetry countings. We found that there was an excellent correlation between signals from in vivo CLI and ex vivo radioactivity (r 2 = 0.95) (Fig. 3d), as well as between signals from ex vivo CLI and ex vivo radioactivity (r 2 = 0.97) (Fig. 3e).
Due to the depth-penetrating limitation of optical imaging, disparity between in vivo and ex vivo data often exists. However, our data demonstrated a good correlation between in vivo CLI and ex vivo CLI (r 2 = 0.96) (Fig. 3f). Taken together, our data suggest that in vivo CLI imaging of BAT is reliable.

Monitoring BAT Activity using CLI
After confirmation of CLI feasibility and reliability for BAT imaging with 18 F-FDG, we utilized this method for monitoring BAT activity. NE treatment and cold exposure are the most used methods for BAT activation [8,10,39,40]. First, we compared BAT activity in the same group of mice with and without NE treatment under short (5 minute) isoflurane anesthesia. As expected, we found that BAT activity under NE-treated condition was significantly higher (1.23-fold) than without NE treatment ( Fig. 4a, b). Similar results were observed under the long (60 minute) isoflurane anesthesia. Interestingly, the difference in BAT activity between NE-treated and non-treated animals was even larger under long isoflurane anesthesia (60 minute) than under short (5 min) isoflurane anesthesia (2.47 fold, Fig. 4c, d). PET imaging of human subjects injected with 18 F-FDG revealed that the uptake of 18 F-FDG in BAT was higher under cold exposure than at room temperature [3,8,42]. In this report, we found that there was a 39% increase of 18 F-FDG uptake in the BAT of animals stimulated with cold exposure (Fig. 4e, f). It has also been reported that different anesthesia regimens have significant effect on BAT activity [10,41,43]. Fueger et al. reported that 18 F-FDG uptake in BAT was significantly reduced after 1 hour of ketamine anesthesia [41]. In the next study, we compared CLI signal of 18 F-FDG accumulation in mice under different anesthesia regimens. We compared CLI signal from mice subjected to isoflurane or ketamine/xylazine anesthesia. One group of mice was subjected to isoflurane anesthesia for only for a short period time needed for injection and imaging (about 5 minutes). After complete clearance of the previous 18 F-FDG dose, the same group was imaged again under ketamine/xylazine anesthesia for about 70 minutes. Our imaging data revealed that there was a 54% decrease in 18 F-FDG BAT uptake in the group anesthetized with ketamine compared to the isoflurane group (Fig. 4g, h). Our results were similar to Fueger's report, in which 18 F-FDG uptake by BAT was dramatically depressed under long anesthesia treatment [41].

Spectral Unmixing and Multispectral Cerenkov Luminescence Tomography
In this report, we collected CLI signal with multiple filters, and these data were used for spectral unmixing and multispectral Cerenkov luminescence tomography [31]. 18 F-FDG (11.1 MBq) was injected in mice and multispectral images of the animals' dorsal side were acquired 60 minutes after the injection with 20 nm-wide filters at 580, 600, 620, 640, 660 and 680 nm (raw images are shown in Fig. S3). Spectral unmixing was conducted with commercial software package to separate two components (BAT and unspecific signals). From Fig. 5a, it is clear that the unmixed component #1 (Unmix #1) represented unspecific CLI from 18 F-FDG, with no particular area highlighted. The spectrum (blue line in Fig. 5d) further confirmed that the Unmix #1 represented an unspecific CLI signal, because the spectrum matched with the emission spectrum of 18 F in pure media, in which the CLI intensity is inversely correlated with the square of the wavelength [18,19,20]. This indicates that the Cerenkov emissions in Unmix #1 are from very shallow depths, such as 18 F-FDG accumulation in the skin, as the observed emission spectrum is not affected by tissue absorption. Unmixed component #2 (Unmix #2) reflected the signals from interscapular BAT (Fig. 5b). Notably, the spectrum peak (red line) was around 640 nm and the signal considerably inflated with the increase of the wavelength before reaching the peak, while the intensity of CLI was not dramatically decreased once it reached the peak (red line in Fig. 5d). This phenomenon is probably due to two facts: 1) the light absorption of hemoglobin in blood and cytochrome c in mitochondria for short wavelength CLI (,640 nm;BAT contains more mitochondria and is highly vascularized compared to other nearby tissues [1]); 2) better tissue penetration of the emitted light with longer wavelength.
The 3D reconstruction was conducted with multispectral Cerenkov luminescence tomography (msCLT), which is based on a set of 2D planar CLI images acquired using a number of narrow bandpass filters. 3D image reconstruction utilizes the distinctive diffuse information at each wavelength [31,44]. The advantage of this method is that it provides depth resolution and localization without requiring multiple views of the animal. Recently, several other groups have also demonstrated the feasibility of 3D CLI reconstruction [30,45,46,47]. In the process of msCLT, the 1/l 2 wavelength dependence of the Cerenkov spectrum [18,19,20] was incorporated in the model of multispectral diffuse light propagation. The wavelength-dependent scattering and attenuation coefficients were selected depending on the imaged tissues [44]. The reconstructed 3D images revealed that CLI signal originated from shallow locations (Fig. 6b), and that a significant portion of the signal was coming from interscapular BAT (Fig. 6a-d). This signal was particularly obvious in coronal images that clearly displayed two lobes of BAT (Fig. 6a,  d). Notably, the contour was very similar to the physical triangle shape of BAT shown in Fig. 6e.

Discussion
BAT or brown fat, widely known as 'good fat,' has been considered as a furnace in the body for burning excess calories. The most distinct characteristics of BAT include a large number of mitochondria, abundant UCP-1 (uncoupling protein-1) expression, and numerous small oil droplets in a single cell, as well as significant vascularization of BAT tissue [7,10,12,48,49]. These characteristics strongly indicate that BAT plays important roles in metabolism and energy expenditure under both healthy and disease status. In humans, BAT is highly abundant in embryonic and early postnatal stages, but is drastically reduced or is considered to have no physiologic relevance in adult humans [1,2,3]. However, the importance of BAT has recently ''reemerged'' in new studies using PET imaging. PET images have shown that BAT is still present in adults in the upper chest, neck and other locations [7,10,12]. Recently, Cypess et al. imaged and analyzed 3,640 patients and showed that BMI (body mass index) inversely correlated to the amount of brown adipose tissue, suggesting that BAT is an important target in obesity and diabetes [7]. Other studies have also demonstrated that both BMI and body fat percentage had a significant negative correlation with BAT, whereas resting metabolic rate correlated positively with BAT [8,17]. Moreover, it has been reported that individual differences in energy expenditure could have significant, long-term effects on body weight, and that relatively low energy expenditure predicts a weight gain [8,17]. Recently Nagajyothi et al. suggested that BAT is one of the targets for some parasite infection [50], while Herrero et al. indicated that BAT is related to inflammation [51]. There are indications that BAT has great significance during the process of ageing [11] and that its activity is closely related to exercise [15,16]. In addition, to improve the therapy of obesity and diabetes, increasing efforts have been put into harnessing the benefits of BAT. These efforts include the engineering and transplantation of BAT and the promotion of BAT mass by drug treatment [12,52].
Given the importance of BAT for various diseases, we believe that new imaging techniques would be highly beneficial for its studies. Currently, the most widely used imaging method for BAT is PET imaging with 18 F-FDG. PET and CLI imaging both have advantages and disadvantages in terms of cost, sensitivity, spatial and temporal resolution, high throughput and handiness. The advantages of CLI include its low cost imaging system, high sensitivity, potential high spatial resolution with certain radionuclides [20], capacity for high throughput, and ease of learning and usage. Its major disadvantages include tissue penetrating limitation and low sensitivity for deep targets [26,35,36].
For small animal imaging, the obvious benefits of CLI include a low cost of the imaging system, fast image acquisition for 2D planar imaging, and high throughput capacity. Although CLI signal from 18 F-FDG is not very strong, the highly sensitive, cooled camera (290uC) in optical systems could make each imaging acquisition time considerably shorter than that of PET imaging. In our case, high quality CLI images with 18 F-FDG (7.4-11.1 MBq with i.v. injection) were obtained using a 2-minute acquisition time, while PET imaging normally required more than 5 minutes for each imaging session. However, advanced CLI techniques such as multi-spectral imaging and 3D tomography would normally need longer acquisition times (10-30 minutes). Recently, studies have indicated that the sensitivity of CLI is comparable to PET for shallow targets such as xenografted tumors, lymph nodes and the thyroid [18,20,34,54]. Our data also indicated that CLI is a very sensitive method for BAT imaging both in vivo and ex vivo. CLI signal from BAT was detectable at even two hours after 10.3 MBq 18 F-FDG injection (Fig. 1b,c) and ex vivo biodistribution indicated that 7.4 KBq 18 F-FDG could produce considerable CLI signal (Fig. S1).
Biodistribution data measured by radioactivity counting and CLI were very similar. Heart and BAT were the tissues with the highest 18 F-FDG uptake in both modalities. However, the CLI signal ratio of BAT/heart was higher than that of radioactivity counting (2.92 vs 1.76, Fig. 2a,b). This was probably due to the low CLI signal from the heart, in which a large amount of blood could absorb the emitted CLI light. CLI is a planar imaging method, which collects signals from the body surface; therefore, it is necessary to verify whether the CLI signal at the interscapular site is from BAT. Our biodistribution data indicated that the majority CLI signal at the interscapular site was from BAT, and a further BAT removal experiments validated this indication. Our correlation studies between in vivo CLI, ex vivo CLI, and radioactivity countings indicated that BAT imaging with CLI was reliable. Excellent correlation of in vivo CLI and ex vivo CLI from dissected BAT again suggested that in vivo CLI signal at the interscapular site was primarily from BAT. Although we did not conduct PET imaging with 18 F-FDG to correlate with our in vivo CLI signal, the radioactivity counting could be considered a reasonable surrogate for PET imaging because both methods reflect the actual amount of radioactive substance in the target tissue.
In human studies, it has been reported that PET imaging signals of BAT deposits with 18 F-FDG varied considerably under different conditions. For instance, only 3%-8% of patients' BAT stores could be clearly visualized with 18F-FDG if no cold or drug stimulation was applied. On the contrary, after cold activation .95% of patients' BAT could be imaged with 18 F-FDG [7,8]. However, we observed that this was not the case for mice, because there was an apparent CLI signal even under non-treated conditions (Fig. 1b). This is probably due to the certain level of BAT activation in mice that they maintain to keep their body warm, particularly nude mice. Spectral unmixing is a very useful technique in fluorescence imaging, which could enable the removal of autofluorescence from a subject. However, it is not often used in cases of bioluminescence imaging because bioluminescence background from non-luciferase expressing tissue is always negligible. Nonetheless, the uptake of 18 F-FDG in mice is not highly target-specific (even though heart, BAT, and brain are the major targets) and some unspecific CLI signals are detectable. We found that this unspecific uptake problem could be solved with the spectral unmixing technique. The unmixed spectrum of unspecific 18 F-FDG in skin and superficially in muscle was very similar to the CLI spectrum of pure 18 Fin water [18,20]. The CLI spectrum of BAT reflected the actual surroundings of BAT, which contain abundant heme proteins, which form hemoglobin in blood and cytochrome C in mitochondria. Our 3D reconstruction was conducted with a commercial optical system using the diffusive properties of different wavelengths. The method allowed us to avoid using a complicated optical imaging system that requires acquisition of multiple-angle view images and therefore could be easily operated and accessed. The 3D images indicated that the majority of CLI signals originated from shallow locations, but not from the heart or other organs. This result was consistent with our biodistribution studies. It is widely known that 2D planar optical imaging is semi-quantitative [53], so is 2D CLI used in this report. Although 3D CLI tomography imaging could provide better quantification, and great efforts have been put into different reconstruction methods [31,45,54], commercially available software packages are still not available yet. Therefore the accessibility of 3D CLI is the bottleneck for wide application of this advanced technology. Hopefully, this limitation could probably be overcome in the near future.
For the very recent development of this technology, it is very exciting that the first human CLI imaging has been successfully demonstrated [55]. Conceivably, CLI imaging of BAT in the neck area in humans is possible due to its shallow location.
In summary, we demonstrated that CLI with 18 F-FDG could be used as a reliable method to image BAT and to monitor its activation. This method is particularly useful for small animal models where BAT location is ideal for optical registration. Compared to 18 F-FDG PET imaging, CLI is much cheaper, faster, and can be used for in vivo high throughput screening as well. In addition, our study also showed that 3D tomography of CLI is feasible and that 3D volume quantification is possible for future studies. For small animal imaging, we believe that CLI imaging of BAT could be a useful complementary tool to PET imaging in small animals for researchers investigating BAT.

Experiments
Female nu/nu mice 4-8 weeks of age were purchased from Massachusetts General Hospital Radiation Oncology breeding facilities. All experimental procedures were approved by the Subcommittee on Research Animal Care at Massachusetts General Hospital. CLI imaging was performed using an IVISHSpectrum animal imaging system (Perkin Elmer/Caliper LifeSciences, Hopkinton, MA). Image analysis was conducted using LivingImageH 4.2 software. The 18 F-FDG images were not decay corrected for all quantification because our comparisons between different animal groups were made at the same timepoints, and acquisition parameters were the same. 18 F-FDG was purchased from IBA Molecular.

Feasibility Study
Mice (n = 3) were anesthetized with isoflurane balanced with oxygen for 5 minutes and injected with 10.3 MBq of 18 F-FDG intravenously. Injected mice were then subjected to luminescence imaging at 30, 60, and 120 minutes after 18 F-FDG injection with the following parameters: open filter, f = 1, bin = 8, FOV = D, and exposure time = 120 s.

Validation of BAT Location by CLI and Biodistribution Studies
Mice (n = 3) were anesthetized with isoflurane balanced with oxygen for 5 minutes and injected with 10.3 MBq of 18 F-FDG intravenously. Mice were sacrificed at 60 minutes after injection. The skin from the interscapular area was removed and mice underwent imaging before and after BAT removal, using the same parameters as listed above in the feasibility study section. After imaging, organs were dissected, collected and weighed, and subjected to optical imaging (open filter, f = 1, bin = 8, FOV = D, and exposure time = 120 s) and to radioactivity counting with dosimeters. The distribution of signals was normalized to the weight of the tested organs.

Reliability Studies with Ketamine Anesthesia and NE Treatment
Nude mice (n = 8) were divided into two groups (n = 4 each). One group was injected with norepinephrine (NE) (50 uL, 10 mM) intraperitoneally. The second group served as a noninjected control. After 30 minutes, both groups were injected intraperitoneally with ketamine/xylazine and kept under anesthesia for the following 60-70 minutes at room temperature. Once mice were anesthetized, 18 F-FDG (8.1 MBq) was intravenously injected into each mouse. Mice were imaged at 60 minutes after 18 F-FDG injections, using the same parameters as for the feasibility study. For the correlation study, mice were sacrificed immediately after imaging, BAT was excised, and CLI imaging and a dosimeter counting were performed.

Monitoring Activation with NE and Cold Exposure Under Isoflurane Anesthesia
A similar procedure for NE activation and cold exposure was followed as above, except isoflurane was used and anesthesia time lasted for 5 minutes before each image acquisition (n = 4). For long isoflurane anesthesia (60 minutes), mice were kept in an isoflurane induction chamber after 18 F-FDG injection. For cold exposure study, mice were placed in a cold room (4uC) for 4 hours before 18 F-FDG injection and returned to the cold room once recovered from anesthesia until the images were acquired. The body temperatures of the mice in the cold room were measured with a rectal thermometer and we found that their temperatures were about 30uC.

Spectral Unmixing and Multispectral Cerenkov Luminescence Tomography Studies
Mice were anesthetized for 5 minutes with isoflurane followed by intravenous injection of 11.1MBq 18 F-FDG. Multispectral images were acquired with the following parameters: f = 1, bin = 16, acquisition time = 300s per filter, emission filters = 580, 600, 620, 640, 660 and 680 nm (raw images are shown in Fig. S2). Spectral unmixing was conducted with Living Imaging 4.31 software from Caliper, a Perkin Elmer Company, and two components and automatic unmixing were used. A 3D reconstruction was conducted according to the method reported by Kuo et al. [31,44] and using in-house software from Caliper, a Perkin Elmer Company. The Cerenkov emission spectrum was incorporated into the model of diffuse light propagation. Tikhonov regularization was applied in the non-negative least squares optimization of the residuals, and the surface tomography generated from structure light imaging was used for 3D image co-registration. Figure S1 Representative CLI images of dissected tissues (n = 3). 1) liver, 2) heart, 3) lung, 4) brain, 5) muscle, 6) kidney, 7) spleen, 8) intestine, 9) bladder, 10) skin, 11) blood, 12) stomach, 13) white fat from belly, 14) BAT. (TIF) Figure S2 Quantitative analysis of signals of the NEtreated group and the control group. Radioactivity reading (a), in vivo CLI signals (b), and ex vivo CLI signals (c) (n = 4 for each group). (TIF) Figure S3 Raw images for spectral unmixing and multispectral Cerenkov luminescence tomography imaging.