- Original research
- Open Access
18F-FDG-labeled red blood cell PET for blood-pool imaging: preclinical evaluation in rats
EJNMMI Research volume 7, Article number: 19 (2017)
Red blood cells (RBCs) labeled with single-photon emitters have been clinically used for blood-pool imaging. Although some PET tracers have been introduced for blood-pool imaging, they have not yet been widely used. The present study investigated the feasibility of labeling RBCs with 18F-2-deoxy-2-fluoro-D-glucose (18F-FDG) for blood-pool imaging with PET.
RBCs isolated from venous blood of rats were washed with glucose-free phosphate-buffered saline and labeled with 18F-FDG. To optimize labeling efficiency, the effects of glucose deprivation time and incubation (labeling) time with 18F-FDG were investigated. Post-labeling stability was assessed by calculating the release fraction of radioactivity and identifying the chemical forms of 18F in the released and intracellular components of 18F-FDG-labeled RBCs incubated in plasma. Just after intravenous injection of the optimized autologous 18F-FDG-labeled RBCs, dynamic PET scans were performed to evaluate in vivo imaging in normal rats and intraabdominal bleeding models (temporary and persistent bleeding).
The optimal durations of glucose deprivation and incubation (labeling) with 18F-FDG were 60 and 30 min, respectively. As low as 10% of 18F was released as the form of 18F-FDG from 18F-FDG-labeled RBCs after a 60-min incubation. Dynamic PET images of normal rats showed strong persistence in the cardiovascular system for at least 120 min. In the intraabdominal bleeding models, 18F-FDG-labeled RBC PET visualized the extravascular blood clearly and revealed the dynamic changes of the extravascular radioactivity in the temporary and persistent bleeding.
RBCs can be effectively labeled with 18F-FDG and used for blood-pool imaging with PET in rats.
Nuclear medicine techniques using red blood cells (RBCs) labeled with several single-photon emitters such as 99mTc have been used for blood-pool imaging (BPI). The purposes of BPI include the detection of gastrointestinal bleeding [1, 2], evaluation of cardiac function [3, 4], localization of hemangiomas [5, 6], and regional cerebral blood volume measurement . RBCs would be a more suitable tracer for BPI than radionuclide-labeled plasma proteins because plasma proteins tend to leak into extravascular spaces . Since Fisher et al. reported the first human study of 99mTc-labeled RBCs for splenic radionuclide imaging 50 years ago , 99mTc-labeled RBC scintigraphy has been clinically used for BPI. Furthermore, single-photon emission computed tomography/computed tomography (SPECT/CT) improves the anatomical information of 99mTc-labeled RBC imaging .
Although positron emission tomography (PET) has better image quality than scintigraphy and SPECT, blood-pool agents for PET are limited. Carbon monoxide (CO) labeled with 11C or 15O has been applied to RBC imaging with PET [11, 12], but the short half-life of these radionuclides prevents their widespread use. Fluorine-18 seems more suitable for PET BPI in terms of the longer half-life and shorter positron range . To our knowledge, there have been a few reports which demonstrated the labeling of RBCs with 18F-labeled compounds: 18F-sulfonamide derivative  and 18F-N-succinimidyl 4-18F-fluorobenzoate (18F-SFB) . In these two reports, RBC PET was successful in evaluation of cardiac function or blood volume quantification, respectively.
Fluorine-18-2-deoxy-2-fluoro-D-glucose (18F-FDG) is the most available PET tracer in the world. Fluorine-18-FDG-labeled white blood cells (WBCs) have already been clinically used as an inflammation-seeking agent [15,16,17,18]. Due to the absence of nuclei or mitochondria, glucose is the only energy substrate for RBCs; thus, we speculated that RBCs could be also labeled with 18F-FDG for imaging. There has been evidence of transporting 18F-FDG into RBCs in an equilibrium state [19, 20]. The aims of the present study were to determine an optimal labeling procedure for 18F-FDG-labeled RBCs and to demonstrate the suitability of the RBC preparation for BPI using in vivo rat imaging.
The entire experimental protocols were approved by the Keio University Institutional Animal Care and Use Committee and performed in accordance with the Institutional Guidelines on Animal Experimentation at Keio University. Healthy male F344/Jcl rats were purchased from Clea Japan Incorporation. The rats were given standard rat chow and tap water ad libitum.
RBC preparation for in vitro studies
After a 3-h fasting period, the rats (weight, 188.7 ± 16 g) were anesthetized with isoflurane. The inferior vena cava (IVC) was exposed through an abdominal incision. A 23-gauge needle was placed in the IVC, and heparin (1000 IU/kg body weight) was administered to prevent blood coagulation. Thirty seconds later, the blood (4 ml) was slowly withdrawn from the IVC. Blood glucose concentration was measured with a glucometer (Accu-Chek Aviva; Roche Diagnostics Co., Ltd., Japan). The blood was centrifuged at 500g for 10 min at 4 °C. The supernatant (plasma) was stored for subsequent post-labeling stability studies. The buffy coat, which contains most of WBCs and platelets, was removed. To eliminate extracellular glucose, the packed RBCs were washed three times in the following way: RBCs were mixed with glucose-free phosphate-buffered saline (PBS) (8 ml; Wako Pure Chemical Industries, Ltd., Japan) and centrifuged at 1000g for 2 min, and the supernatant was removed. After washing, the packed RBC suspension was uniformly resuspended and the hematocrit was measured with the microhematocrit technique after centrifuging at 12,000g for 3 min [21, 22]. Hematocrit was adjusted to 2.5–80% by diluting the packed RBCs with a calculated volume of PBS.
Preparation of 18F-FDG
Fluorine-18-FDG was produced in a clinical routine setup on-site. The specific radioactivity at the time of labeling was approximately 500 GBq/μmol. The osmolarity of 18F-FDG solution was adjusted to prevent some RBCs from rupture because of the hyposmosis of original 18F-FDG solution (less than 4 mOsm/L). As previously performed in the study of 18F-FDG-labeled WBCs by Osman et al. , 11 μL of 10X PBS (2800 mOsm/L; Wako Pure Chemical Industries, Ltd., Japan) was added to 100 μL of 18F-FDG solution.
Labeling efficiency analysis
We considered that labeling efficiency (LE) of 18F-FDG-labeled RBCs would be influenced by the following possible factors: depletion of intracellular glucose before labeling, hematocrit for labeling, and incubation (labeling) time with 18F-FDG.
We hypothesized that LE could be increased by incubating RBCs in glucose-free PBS at 37 °C before labeling, which can reduce intracellular glucose concentration. To investigate the effect of glucose deprivation before labeling, the prepared RBC suspension (70% hematocrit, 100 μL) was incubated at 37 °C for 0–120 min. The incubated RBC suspension was mixed with 18F-FDG solution (12.0 ± 1.7 MBq, 15.3 ± 0.3 μL, n = 4) and incubated for 30 min at 37 °C for labeling. To eliminate extracellular 18F-FDG, the labeled RBCs were washed three times at 4 °C with Hanks’ balanced salt solution (HBSS) (Wako Pure Chemical Industries, Ltd., Japan) containing glucose (100 mg/dL). The primary radioactivity of 18F-FDG and the radioactivity of the labeled RBCs were measured with a dose calibrator (Curiemeter IGC-7; Aloka, Japan). Then, LE was calculated as a percentage by dividing the radioactivity of the labeled RBCs by the primary radioactivity with decay correction.
The relationship between hematocrit for labeling and LE was analyzed. The hematocrit of the prepared RBC suspension was adjusted to 2.5–80%. After a 60-min incubation at 37 °C for reducing intracellular glucose concentration before labeling, each hematocrit suspension (100 μL) was mixed with 18F-FDG solution (15.0 MBq, 14.6 μL) and incubated for 30 min at 37 °C for labeling. Washing, radioactivity measurement, and LE calculation were performed following the same procedure as described above. In addition, the relationship between the added radioactivity of 18F-FDG (7.3–20.1 MBq) and the radioactivity of labeled RBCs was analyzed.
The effect of the labeling (incubation) time with 18F-FDG on LE was investigated. The prepared RBC suspension (100 μL, 70% hematocrit) was incubated for 60 min at 37 °C to reduce intracellular glucose concentration before labeling. The RBC suspension was mixed with 18F-FDG solution (11.1 ± 0.7 MBq, 14.3 ± 3.2 μL, n = 3). The labeling times with 18F-FDG at 37 °C were varied from 0 to 60 min at an interval of 5 min. Washing, radioactivity measurement, and LE calculation were performed following the same procedure as described above. Based on the results of these analyses, the optimal conditions for labeling RBCs with 18F-FDG were determined and then further experiments were performed.
Post-labeling stability of 18F-FDG-labeled RBCs
The post-labeling stability was assessed by calculating a release fraction of radioactivity from 18F-FDG-labeled RBCs. The washed RBC suspension (1.5 ml, 80% hematocrit, n = 4) was incubated for 60 min at 37 °C to reduce intracellular glucose concentration before labeling. The RBC suspension was mixed with 18F-FDG (more than 100 MBq) and incubated for 30 min at 37 °C for labeling. To eliminate extracellular 18F-FDG, the labeled RBCs were washed three times with HBSS at 4 °C. The radioactivity of 18F-FDG-labeled RBCs was measured with the dose calibrator. The labeled RBC suspension was diluted with the plasma separated soon after blood sampling, and its hematocrit was adjusted to 40%. The labeled RBC suspension (200 μL, 40% hematocrit) was incubated for 0–180 min at 37 and 0 °C. After each incubation time, the labeled RBC suspension was cooled and uniformly resuspended. The whole RBC suspension (10 μL) was sampled for radioactivity measurement. The remnant RBC suspension was centrifuged at 1000g for 2 min, and the supernatant (10 μL) was also sampled. The whole RBC suspension and the supernatant were simultaneously measured with a well-type scintillation counter (ARC-380CL, Aloka, Japan). The release fraction was calculated according to the formula,
, where hematocrit was 40%.
In addition, extracellular glucose concentration of the supernatant during the 180-min incubation was measured with a glucometer to check the uptake ratio of glucose by RBCs at 37 and 0 °C.
To estimate the chemical form of 18F released from 18F-FDG-labeled RBCs, thin-layer chromatography (TLC) was performed. Fluorine-18-FDG-labeled RBC suspension diluted with plasma (40% hematocrit, 200 μL) was prepared following the same procedure used for the stability study described above. After a 60-min incubation of the 18F-FDG-labeled RBC suspension at 37 °C, it was centrifuged at 1000g for 2 min at 4 °C. The supernatant was spotted on to silica gel TLC strips (4 × 8 cm, Merck, Darmstadt, FRG). The packed RBCs were washed three times with HBSS at 4 °C to eliminate extracellular radioactivity, and the labeled RBCs were completely lysed with distilled water. The lysate was spotted onto another TLC strip. Original 18F-FDG solution was spotted as an authentic sample. Acetonitrile/water (v/v = 95:5) was used as eluent. Chromatograms were measured using a Typhoon FLA 9000 imager (GE Healthcare Life Sciences). Fluorine-18-FDG and 18F-FDG-6-phosphate were identified by their Rf values (0.37 and 0, respectively) .
Preparation of labeled RBCs for PET imaging
After a 3-h fasting period, the rats were anesthetized with isoflurane. The blood (400 μL) was slowly withdrawn from the cervical vein using a heparinized syringe with a 27-gauge needle. After blood sampling, the rats were recovered from anesthesia and replaced in their cages without food. The blood was centrifuged at 500g for 5 min at 4 °C, and the buffy coat was removed. The packed RBC suspension (100 μL, 80% hematocrit) was washed three times with PBS. After a 60-min incubation in glucose-free PBS at 37 °C for reducing intracellular glucose concentration, the RBCs was mixed with 18F-FDG solution (20.0 ± 8.4 MBq) and incubated for 30 min at 37 °C for labeling. After labeling, 18F-FDG-labeled RBCs were washed three times with HBSS at 4 °C to eliminate extracellular 18F-FDG. The LE was calculated with decay correction. The packed labeled RBC suspension (100 μL) was diluted with HBSS, and the total volume was adjusted to 400 μL (20% hematocrit). The obtained labeled RBC suspension was cooled and preserved at 0 °C until injection. In addition, the labeled RBCs were observed with a microscope to evaluate their morphological abnormality.
PET imaging of normal rats
The rats (169 ± 18g, n = 5) were anesthetized again and maintained with isoflurane throughout the imaging procedure. Imaging was performed using a small-animal PET system (ClairvivoPET; Shimadzu Corporation, Japan) . The rats were placed in a supine position on a fixation plate in the PET scanner. A transmission scan with an external 137Cs point source (22 MBq) was performed for attenuation correction. Autologous 18F-FDG-labeled RBC suspension (10.5 ± 3.7 MBq, 400 μL, 20% hematocrit, rewarmed at room temperature) was injected via the lateral tail vein. Image acquisition was simultaneously started, and list-mode data were acquired for 120 min. The rectal temperature was kept at 36–38 °C by heating. The list-mode data were reconstructed into a dynamic sequence (27 frames, 3 × 10, 5 × 30, 2 × 60, 11 × 300, and 6 × 600 s) using 3D-DRAMA (dynamic row-action maximization-likelihood algorithm) with decay correction. The matrix size was 128 × 128 × 213 pixels.
Intraabdominal bleeding models
We imaged intraabdominal bleeding models of rats as a potential use of 18F-FDG-labeled RBC PET. Before PET imaging, glycerin enema (1 mL) was transanally injected into the colon for defecation. After a transmission scan, autologous 18F-FDG-labeled RBC suspension (10 MBq, 400 μL) was intravenously injected, and image acquisition was simultaneously started. List-mode data were acquired for 40 min. In a steady-state of the BPI (20–25 min after injection), a transanal puncture of the colonic wall was manually given with an 18-gauge intravenous needle to induce hemorrhage into the abdominal cavity. In the present study, two kinds of bleeding models were imaged: persistent and temporary bleeding models. To model a persistent bleeding rat (171 g, n = 1), heparin (1000 IU/kg body weight) was injected via the tail vein just before injection of 18F-FDG-labeled RBCs, whereas no heparin was used for a temporary bleeding model (170 g, n = 1). After PET imaging, CT was performed using a micro CT system (R-mCT; Rigaku, Japan) to localize the extravascular blood inside the abdominal cavity. CT parameters were as follows: X-ray source, 90 kV/100 μA; rotation, 360°; exposure time, 17 s; and voxel size, 133 × 133 × 282 μm.
The reconstructed images were analyzed using PMOD version 3.80 (PMOD Technologies Ltd, Switzerland). In the images of normal rats, volumes of interest (VOIs) were placed in each organ, and the radioactivity was expressed as the percentage of injected dose per gram (%ID/g). Time-activity curves (TACs) for the atrium, lung, liver, brain, spleen, kidney, and urinary bladder were obtained.
In order to measure the radioactivity of bleeding in the intraabdominal bleeding models, image subtraction was performed between the post-bleeding images (38–40 min after injection) and the pre-bleeding images (10–20 min after injection) with an algebra tool of PMOD. Negative values of the pixels in the subtracted images were all replaced to zero value. Then, the total radioactivity of bleeding during PET imaging was measured as the percentage of injected dose (%ID) after excluding radioactivity of the urinary bladder.
Quantitative data were expressed as mean ± SD. Spearman’s rank correlation coefficient was used to assess the quality of linear correlations using the SPSS software package (version 22.0, SPSS Inc., IBM, Chicago, USA). A P value of less than 0.05 was considered statistically significant.
The blood glucose concentration soon after blood sampling was 232 ± 30 mg/dL. In Fig. 1, LE under various circumstances is summarized. The LE increased with the incubation time in PBS before labeling and was 37.6% in 0 min and 76.7% in 60 min (Fig. 1a). The higher the hematocrit for labeling is, the higher the LE is (Fig. 1b). At this time, there were technical difficulties accurately measuring LE when hematocrit was over 80% because of the high viscosity and the presence of dried-up RBCs around fluid surface during a long incubation. Even though LE continued to rise over labeling time (Fig. 1c), the loss of radioactivity exceeded the increase in LE after 30–35 min and the net radioactivity began to decrease after this time (Fig. 1d). There was a positive correlation between 18F-FDG-added and 18F-FDG-labeled RBCs (Additional file 1: Figure S1). Based on these results, we determined that the optimal labeling conditions were as follows: glucose depriving time was 60 min, hematocrit for labeling was 70%, and labeling (incubation) time was 30 min.
Post-labeling stability of 18F-FDG-labeled RBCs
In Table 1, LE of 18F-FDG-labeled RBCs by means of the optimized labeling procedure is shown. The obtained radioactivity of 18F-FDG-labeled RBC suspension (1.5 mL) was 89 ± 26 MBq, and the LE was 69.3 ± 13.3%. Figure 2 summarizes the post-labeling stability of 18F-FDG-labeled RBCs. The release fraction of a chemical form of 18F increased constantly for 3 h at 37 °C; no release was seen at 0 °C (Fig. 2a). The release fractions at 37 °C in 60, 120, and 180 min incubation were 10.1, 15.8, and 20.5%, respectively, which were larger than we expected. TLC of extra- and intracellular fluid at 60 min of incubation showed the 18F-FDG ratio of extracellular fluid (release) was 92.6%, while that of intracellular fluid (hemolysis) was 4.7% (Fig. 2b). Extracellular glucose concentration gradually decreased at 37 °C but did not change at 0 °C (Additional file 1: Figure S2).
Labeling for in vivo imaging
Labeling RBCs with 18F-FDG for in vivo imaging was performed with the optimized procedure as shown in Fig. 3. The average time from blood sampling to intravenous injection of 18F-FDG-labeled RBC suspension was approximately 125 min. In microscopic images, 18F-FDG-labeled RBCs appeared normal and no aggregation of RBCs nor RBCs with abnormal shapes (e.g., spherocytes, acanthocytes, or schistocytes) were seen (Additional file 1: Figure S3). The radioactivity of the obtained 18F-FDG-labeled RBC suspension (400 μL, 20% hematocrit) were 11.2 ± 3.9 MBq, and the LE was 71.7 ± 10.2% (n = 4).
PET imaging of normal rats
The maximum-intensity-projection images revealed that the cardiac space and the vessels of whole bodies showed a strong accumulation of 18F-FDG-labeled RBCs (Fig. 4a). TACs of the organs showed that the radioactivity of the most organs was relatively constant up to 120 min (Fig. 4b), suggesting that our procedure was appropriate for BPI. The intraatrial radioactivity of 60 min decreased only 5.6% compared to that of 5–10 min. Meanwhile, slight urinary excretion was seen. The splenic radioactivity was higher than the hepatic radioactivity and lower than the pulmonary radioactivity during 30 min after injection.
Intraabdominal bleeding models
Dynamic PET images revealed the appearance of high accumulation sites in the abdomen soon after the puncture of the colon wall, suggesting the extravasation of the tracer due to bleeding (Figs. 5a and 6a). Extravascular blood was not identified in the CT image (Figs. 5b and 6b). The TAC of the extravascular blood in the temporary bleeding model (without heparin) rose soon after puncture of the colon wall and reached a plateau in 4 min, while the TAC in the persistent model (with heparin) rose continuously (Figs. 5c and 6c).
To our knowledge, this is the first study demonstrating the feasibility of labeling RBCs with 18F-FDG. In order to apply 18F-FDG-labeled RBC PET to human study, optimization or standardization of labeling procedure is crucial in terms of the accuracy of 18F-FDG-labeled RBC PET for BPI. Therefore, we sought the optimal labeling procedure to achieve the highest LE and stability by measuring LE in different conditions. In the optimized labeling protocol, 18F-FDG-labeled RBC PET revealed high retention of the tracer in the cardiovascular system for at least 120 min in normal rats. In the intraabdominal bleeding models, 18F-FDG-labeled RBC PET visualized the extravascular blood more clearly than CT and revealed the different patterns of the extravascular radioactivity between the temporary and persistent bleeding models.
We considered that high LE could be achieved by depriving glucose from RBCs. Glucose deprivation reduces intracellular glucose concentration. In addition, a glucose concentration gradient across the membrane is the driving force to transport glucose via glucose transporter-1 on the plasma membrane of RBCs . Taken together, this pre-labeling preparation can boost the uptake of glucose or 18F-FDG into RBCs. Indeed, our results showed that glucose deprivation for up to 60 min significantly improved the LE (Fig. 1a). Considering the balance between the LE and the potential cell damage due to prolonged glucose deprivation, the duration of glucose deprivation was set at 60 min in subsequent studies. Higher hematocrit was suitable for achieving higher LE (Fig. 1b). However, it was practically difficult to uniformly mix high-hematocrit RBC suspension (over 80% hematocrit, 100 or 200 μL) with 18F-FDG solution (10–20 μL) due to high viscosity. In addition, some RBCs in high-hematocrit RBC suspension dried up around fluid surface during long incubation. Therefore, hematocrit was set at 70% in other labeling studies. LE steadily increased during the incubation with 18F-FDG, reaching a plateau in 50 min (Fig. 1c). Consequently, the total amount of radioactivity in the RBCs showed a peak from 30 to 40 min due to beta decay of 18F (Fig. 1d). As a result, the optimal incubation (labeling) time with 18F-FDG was considered to be 30 min.
In the stability studies in vitro, 18F-FDG-labeled RBCs gradually released 18F-FDG at 37 °C for at least 3 h (Fig. 2). Since the released 18F-FDG would be excreted in urine or taken up by extravascular tissues after injection, BPI with 18F-FDG-labeled RBCs should be performed as early as possible after equilibrium in the blood is achieved. While the retention rate of 18F-FDG in the in vitro assessment was 89.9% at 60 min (Fig. 2a), that of the stability studies in the in vivo assessment was 94.4% at 60 min (Fig. 4b). Therefore, we concluded that 18F-FDG-labeled RBCs were relatively stable in vivo and were suitable for BPI.
We found that keeping the labeled RBCs at 0 °C prevented the 18F-FDG release. Thus, the preparation after the incubation with 18F-FDG should be performed at 0° in case of a long time interval between the preparation and injection. Actually, we performed pre-injection cooling and rewarming just before injection for in vivo studies.
Based on the results of TLC, the radioactive substances inside 18F-FDG-labeled RBCs during the incubation in plasma were almost all non-FDG (Fig. 2b). Radioactivity in the intracellular fluid was likely to represent 18F-FDG-6-phosphate because of the phosphorylation by hexokinase in RBCs. In addition, the fact that RBCs have no radioactivity of glucose-6-phosphatase  would account for the small amount (<5% in 60 min after incubation) of 18F-FDG. However, the exact mechanism for increasing extracellular 18F-FDG (i.e., the labeled RBCs continued to release 18F-FDG) over 180 min was unknown. There might be a glucose-6-phosphatase-independent mechanism as suggested in some tumor cells .
An optimal labeling procedure for the in vivo imaging of rats is shown in Fig. 3. After injecting 18F-FDG-labeled RBCs intravenously, PET images exhibited marked contrast for the blood pool (Fig. 4a). TACs showed that the radioactivity of most organs was nearly unchanged after equilibrium was achieved (Fig. 4b). Since we used in vitro labeling technique, denaturation of the labeled RBCs may be suspected. However, whether 18F-FDG-labeled RBCs were denaturated was unknown because splenic radioactivity was not as high as typically seen in denaturation of the labeled RBCs. Splenic radioactivity depends not only on denaturation of RBCs but also on splenic sequestration of RBCs . Furthermore, splenic sequestration is influenced by adrenergic agonists [28, 29] and isoflurane anesthesia . Thus, the elevation of splenic radioactivity in the present study did not necessarily mean the occurrence of RBC denaturation. Splenic radioactivity of our normal rats during 30 min after injection (Fig. 4b) was almost the same as that of the previous study using 11C-CO-labeled RBCs in rats , in which splenic radioactivity was higher than hepatic radioactivity and lower than pulmonary radioactivity during 30 min after agent administration. Since the labeling procedure of 11C-CO-labeled RBCs is only an inhalation of 11C-CO gas, splenic radioactivity of 11C-CO-labeled RBCs would not be affected by RBC denaturation. Therefore, it is considered that the 18F-FDG-labeled RBCs produced in our procedure would be as stable as 11C-CO-labeled RBCs in rats.
In the intraabdominal bleeding models, the extravascular blood was three-dimensionally identified on the PET images and the dynamic change of extravascular radioactivity was observed (Figs. 5 and 6). Although this was challenging, we tried to measure the change of extravascular radioactivity in the two different intraabdominal bleeding models (Figs. 5c and 6c) because the bleeding rate as well as the bleeding point or volume can influence treatment strategy for intraabdominal bleeding in human practice . The differences in aggressiveness or time course of intraabdominal bleeding could be observed with 18F-FDG-labeled RBC PET, although the quantitative accuracy was not confirmed in the present study. Future evaluation is needed to support this potential way to use 18F-FDG-labeled RBC PET.
Labeling RBCs with 18F-FDG should be of greater value than the other PET tracers because of the overwhelming availability and accessibility of 18F-FDG. However, there are some limitations to our method. First, in vitro labeling is troublesome due to the necessity of blood sampling and labeling procedure, the requirement for a clean space, and the radiation exposure for operators. We may be able to simplify the labeling procedures by reducing the number of washes or by shortening the duration of glucose deprivation. In the present study, we introduced the surest way to obtain BPI using 18F-FDG. Further evaluation regarding simplification of the labeling technique is needed. Second, 18F-FDG-labeled RBC PET has many issues towards clinical applications in contrast to 99mTc-labeled RBC scintigraphy. Although RBCs can be labeled with 99mTc with the in vivo method , it seems to be impossible to label RBCs with 18F-FDG in vivo. Given the short half-life of 18F, it is unlikely that any institution would have a dose available for an emergency GI bleeding study at midnight. Even at daytime, it is not easy to keep 18F-FDG available for unpredictable emergency procedures. Thus, 18F-FDG-labeled RBC PET is challenging for clinical translation at present.
We presented an optimal labeling procedure of 18F-FDG-labeled RBCs for BPI. Among the factors that influenced LE, we found that glucose deprivation dramatically increased LE. Although a slight fraction of 18F-FDG was released from 18F-FDG-labeled RBCs, 18F-FDG-labeled RBC PET images revealed that the cardiovascular system of normal rats was clearly and stably visualized for several hours. In the intraabdominal bleeding models, the extravascular blood was clearly visualized on PET and the dynamic change of extravascular radioactivity was evaluated. There is the need for further research to determine the potential of 18F-FDG-labeled RBCs as a clinical agent for BPI in humans.
Inferior vena cava
Positron emission tomography
Red blood cell
Single-photon emission computed tomography
Volume of interest
White blood cell
Grady E. Gastrointestinal bleeding scintigraphy in the early 21st century. J Nucl Med. 2016;57:252–9. doi:10.2967/jnumed.115.157289.
Winzelberg GG, McKusick KA, Strauss HW, Waltman AC, Greenfield AJ. Evaluation of gastrointestinal bleeding by red blood cells labeled in vivo with technetium-99 m. J Nucl Med. 1979;20:1080–6.
Xie BQ, Tian YQ, Zhang J, Zhao SH, Yang MF, Guo F, et al. Evaluation of left and right ventricular ejection fraction and volumes from gated blood-pool SPECT in patients with dilated cardiomyopathy: comparison with cardiac MRI. J Nucl Med. 2012;53:584–91. doi:10.2967/jnumed.111.096057.
Verani MS, Gaeta J, LeBlanc AD, Poliner LR, Phillips L, Lacy JL, et al. Validation of left ventricular volume measurements by radionuclide angiography. J Nucl Med. 1985;26:1394–401.
Roy SG, Karunanithi S, Agarwal KK, Bal C, Kumar R. Importance of SPECT/CT in detecting multiple hemangiomas on 99mTc-labeled RBC blood pool scintigraphy. Clin Nucl Med. 2015;40:345–6. doi:10.1097/RLU.0000000000000663.
Murata Y, Yamada I, Umehara I, Ishii Y, Okada N. Perfusion and blood-pool scintigraphy in the evaluation of head and neck hemangiomas. J Nucl Med. 1997;38:882–5.
Kuhl DE, Reivich M, Alavi A, Nyary I, Staum MM. Local cerebral blood volume determined by three-dimensional reconstruction of radionuclide scan data. Circ Res. 1975;36:610–9.
Niu G, Lang L, Kiesewetter DO, Ma Y, Sun Z, Guo N, et al. In vivo labeling of serum albumin for PET. J Nucl Med. 2014;55:1150–6. doi:10.2967/jnumed.114.139642.
Fischer J, Wolf R, Leon A. Technetium-99 m as a label for erythrocytes. J Nucl Med. 1967;8:229–32.
Alvarez R, Diehl KM, Avram A, Brown R, Piert M. Localization of splenosis using 99mTc-damaged red blood cell SPECT/CT and intraoperative gamma probe measurements. Eur J Nucl Med Mol Imaging. 2007;34:969. doi:10.1007/s00259-007-0432-3.
Phelps ME, Huang SC, Hoffman EJ, Kuhl DE. Validation of tomographic measurement of cerebral blood volume with C-11-labeled carboxyhemoglobin. J Nucl Med. 1979;20:328–34.
Subramanyam R, Alpert NM, Hoop Jr B, Brownell GL, Taveras JM. A model for regional cerebral oxygen distribution during continuous inhalation of 15O2, C15O, and C15O2. J Nucl Med. 1978;19:48–53.
Herance JR, Gispert JD, Abad S, Victor VM, Pareto D, Torrent E, et al. Erythrocytes labeled with [(18) F]SFB as an alternative to radioactive CO for quantification of blood volume with PET. Contrast Media Mol Imaging. 2013;8:375–81. doi:10.1002/cmmi.1533.
Gheysens O, Akurathi V, Chekol R, Dresselaers T, Celen S, Koole M, et al. Preclinical evaluation of carbon-11 and fluorine-18 sulfonamide derivatives for in vivo radiolabeling of erythrocytes. EJNMMI Res. 2013;3:4. doi:10.1186/2191-219x-3-4.
Osman S, Danpure HJ. The use of 2-[18 F]fluoro-2-deoxy-D-glucose as a potential in vitro agent for labelling human granulocytes for clinical studies by positron emission tomography. Int J Rad Appl Instrum B. 1992;19:183–90.
Forstrom LA, Mullan BP, Hung JC, Lowe VJ, Thorson LM. 18 F-FDG labeling of human leukocytes. Nucl Med Commun. 2000;21:691–4.
Dumarey N, Egrise D, Blocklet D, Stallenberg B, Remmelink M, del Marmol V, et al. Imaging infection with 18 F-FDG-labeled leukocyte PET/CT: initial experience in 21 patients. J Nucl Med. 2006;47:625–32.
Bhattacharya A, Kochhar R, Sharma S, Ray P, Kalra N, Khandelwal N, et al. PET/CT with 18 F-FDG-labeled autologous leukocytes for the diagnosis of infected fluid collections in acute pancreatitis. J Nucl Med. 2014;55:1267–72. doi:10.2967/jnumed.114.137232.
Nahmias C, Wahl LM, Amano S, Asselin MC, Chirakal R. Equilibration of 6-[18 F]fluoro-L-m-tyrosine between plasma and erythrocytes. J Nucl Med. 2000;41:1636–41.
Hays MT, Segall GM. A mathematical model for the distribution of fluorodeoxyglucose in humans. J Nucl Med. 1999;40:1358–66.
Mc GJ, Jones AR, Steinberg AG. The hematocrit of capillary blood. N Engl J Med. 1955;253:308–12. doi:10.1056/nejm195508252530802.
Vogel J, Kiessling I, Heinicke K, Stallmach T, Ossent P, Vogel O, et al. Transgenic mice overexpressing erythropoietin adapt to excessive erythrocytosis by regulating blood viscosity. Blood. 2003;102:2278–84. doi:10.1182/blood-2003-01-0283.
Hamacher K, Coenen HH, Stocklin G. Efficient stereospecific synthesis of no-carrier-added 2-[18 F]-fluoro-2-deoxy-D-glucose using aminopolyether supported nucleophilic substitution. J Nucl Med. 1986;27:235–8.
Mizuta T, Kitamura K, Iwata H, Yamagishi Y, Ohtani A, Tanaka K, et al. Performance evaluation of a high-sensitivity large-aperture small-animal PET scanner: ClairvivoPET. Ann Nucl Med. 2008;22:447–55.
Mueckler M. Facilitative glucose transporters. Eur J Biochem. 1994;219:713–25.
Rose IA, O’Connell EL. The role of glucose 6-phosphate in the regulation of glucose metabolism in human erythrocytes. J Biol Chem. 1964;239:12–7.
Caraco C, Aloj L, Chen LY, Chou JY, Eckelman WC. Cellular release of [18 F]2-fluoro-2-deoxyglucose as a function of the glucose-6-phosphatase enzyme system. J Biol Chem. 2000;275:18489–94. doi:10.1074/jbc.M908096199.
Hannon JP, Bossone CA, Rodkey WG. Splenic red cell sequestration and blood volume measurements in conscious pigs. Am J Physiol. 1985;248:R293–301.
Marini RP, Callahan RJ, Jackson LR, Jyawook S, Esteves MI, Fox JG, et al. Distribution of technetium 99 m-labeled red blood cells during isoflurane anesthesia in ferrets. Am J Vet Res. 1997;58:781–5.
Pavel DG, Zimmer M, Patterson VN. In vivo labeling of red blood cells with 99mTc: a new approach to blood pool visualization. J Nucl Med. 1977;18:305–8.
We thank the CMI Incorporation for supplying 18F-FDG, Yuji Iwata (Shimadzu Corporation, Japan) for the technical support of small-animal PET imaging, Meku Kurose (JAC Corporation, Japan) for the advice of animal rearing, and the Radiation Safety Office staff at the Hospital and School of Medicine in Keio University for setting the experimental environment.
This research project was supported by JSPS KAKENHI Grant Number JP16K10362.
YM, TN, and KT contributed to the study design, preparation of the study, conducting of the measurements, analyzing of the data, drafting of the manuscript, and critical revision of the manuscript. YI contributed to the preparation of the study, conducting of the measurements, and analyzing of the data. CN, KM, and MJ contributed to the study design, drafting of the manuscript, and critical revision of the manuscript. All authors read and approved the final manuscript.
The authors declare that they have no competing interests.
The entire experimental protocols were approved by the Keio University Institutional Animal Care and Use Committee and performed in accordance with the Institutional Guidelines on Animal Experimentation at Keio University.
Additional file 1: Figure S1.
Relationship between the radioactivity of added 18F-FDG and the actual radioactivity of 18F-FDG-labeled RBCs. Positive linear correlation between them was found (some dots overlap). Figure S2. Extracellular glucose concentration during a 180-min incubation of 18F-FDG-labeled RBCs in non-radioactive plasma at 37 °C and at 0 °C (n = 4). Figure S3. Representative microscopic appearance of 18F-FDG-labeled RBCs sampled just before injection. Abnormal RBCs were not identified. (DOCX 330 kb)
Rights and permissions
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.
About this article
Cite this article
Matsusaka, Y., Nakahara, T., Takahashi, K. et al. 18F-FDG-labeled red blood cell PET for blood-pool imaging: preclinical evaluation in rats. EJNMMI Res 7, 19 (2017). https://doi.org/10.1186/s13550-017-0266-3
- Red blood cell
- Blood-pool imaging
- Intraabdominal bleeding