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Logo of nihpaAbout Author manuscriptsSubmit a manuscriptHHS Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
 
Front Biosci. Author manuscript; available in PMC 2009 December 9.
Published in final edited form as:
PMCID: PMC2790725
NIHMSID: NIHMS150048

ADVANCES IN MOLECULAR IMAGING OF PANCREATIC BETA CELLS

Abstract

The development of non-invasive imaging methods for early diagnosis of the beta cell associated metabolic diseases, including type 1 and type 2 diabetes (T1D and T2D), has recently drawn considerable interest from the molecular imaging community as well as clinical investigators. Due to the challenges imposed by the location of the pancreas, the sparsely dispersed beta cell population within the pancreas, and the poor understanding of the pathogenesis of the diseases, clinical diagnosis of beta cell abnormalities is still limited. Current diagnostic methods are invasive, often inaccurate, and usually performed post-onset of the disease. Advances in imaging techniques for probing beta cell mass and function are needed to address this critical health care problem. A variety of currently available imaging techniques have been tested for the assessment of the pancreatic beta cell islets. Here we discuss the current advances in magnetic resonance imaging (MRI), bioluminescence imaging (BLI), and nuclear imaging for the study of beta cell diseases. Spurred by early successes in nuclear imaging techniques for beta cells, especially positron emission tomography (PET), the need for beta cell specific ligands has expanded. Progress in the field for obtaining such ligands is presented. Additionally, we report our preliminary efforts of developing such a peptidic ligand for PET imaging of the pancreatic beta cells.

2. INTRODUCTION

According to the statistics published by the American Diabetes Association (ADA), diabetes is the fifth leading cause of death by disease in the United States, contributing to a total 224,092 deaths in the United States alone in 2002 (1). People with diabetes are at significantly higher risk to develop heart disease and stroke, high blood pressure, blindness, kidney failure, nervous system disease, and other chronic complications that severely affect the life quality of the patients. Being a chronic disease without a cure, diabetes now affects 7.0% of the population in the United States, or 20.8 million children and adults, among which 6.2 million people were undiagnosed. The national medical cost attributable to diabetes was estimated at $132 billion by the ADA in 2002. Both the prevalence of diabetes and the annual expenditures of diabetes-associated care are projected to climb in foreseeable future (1).

Diabetes is hallmarked by high levels of blood glucose caused by lack of insulin production, insulin resistance in peripheral tissues, or both. The insulin producing beta cells that govern glucose homeostasis are located in the islets of Langerhans which make up only 2 – 3 % of all pancreatic tissues. Beta cells represent ~ 80% of the islets, while other types of cells (mainly alpha, delta, and PP cells) contribute to the remaining 20%. In humans, the pancreas is a small elongated pinkish organ in the abdomen neighboring the liver, duodenum, stomach, and spleen.

There are two major forms of diabetes. Type 1 diabetes (T1D), also known as juvenile diabetes, is usually found in children and young adults. It results from a T-cell mediated autoimmune attack on the beta cells (2, 3). Type 2 diabetes (T2D) is the most common form of diabetes accounting for 90 – 95% of all diagnosed cases. T2D begins with insulin resistance in peripheral tissues, a gradual increase in circulating blood glucose that triggers beta cells to release even more insulin, and subsequent failure of beta cells to maintain normal glucose homeostasis (4). While the onset of T1D is directly reflected by the loss of the pancreatic beta cells, T2D consists of multiple metabolic abnormalities leading to hyperglycemia.

It has been shown islet cell autoantibodies are strongly associated with the development of T1D and insulinitis concurs with an inflammatory infiltration of mononuclear cells (5, 6). The appearance of autoantibodies to one or several autoantigens signals the autoimmune pathogenesis of beta cell destruction. Although genetic susceptibility appears to be a prerequisite of developing T1D, studies of identical twins have shown that the concordance rate of the disease is only 40% (7), suggesting that other environmental factors are involved in the initiation and/or progression of T1D. To date, 14 different viruses have been reported to be involved in the development of T1D in humans and animal models (8). Viruses may either trigger beta cell specific autoimmunity leading to diabetes or directly infect and destroy beta cells resulting in T1D.

Several cellular or molecular mechanisms have been reported to be associated with T2D, such as reduced expression of insulin receptors on the surface of insulin-responsive cells (912), alterations in the signal-transduction pathways of insulin action (1316), and abnormalities in biologic pathways normally stimulated by insulin (1720). In addition, mutations in the insulin-receptor gene are responsible for insulin resistance in some people (21).

In spite of the tremendous progress in understanding the basis of diabetes, there is still no known cure. It remains unclear what factors are involved in the disease development and govern the response to therapeutic intervention. With the recent technical innovations in various imaging modalities, molecular imaging is gaining more attention in the basic biomedical sciences and in clinical research and practice (2124). Indeed, non-invasive imaging techniques are revolutionizing the understanding of diseases at the cellular and molecular levels. The ability to non-invasively visualize beta cells would greatly facilitate the development of new methods in the prevention and treatment of diabetes (22, 23).

3. TECHNIQUES FOR IMAGING THE PANCREATIC BETA CELLS

There is considerable interest in using recently developed imaging techniques to monitor the pancreatic beta cells mass and function non-invasively (2249). Conventional magnetic resonance imaging (MRI) and computed tomography can be used to delineate the location of the pancreas in a subject at a spatial resolution of less than 100 micrometers. However, it is extremely difficult, if not impossible, for these two modalities to differentiate the islets of Langerhans from other pancreatic tissues because the pancreas is a highly vascularized soft organ and the islets of Langerhans only represent 2 – 3 % of the pancreas tissues. In order to visualize beta cells in the islets of Langerhans, imaging or contrast agents that recognize the scarcely dispensed beta cells within the pancreas and/or are responsive to their biological functions must be developed.

3.1. Magnetic Resonance Imaging Methods

New methods have been developed in recent years to overcome the sensitivity limit of MRI for the assessment of the pancreatic beta cells. In 2002, Moore and coworkers first reported a sensitivity-enhancing method to distinguish the endocrine from exocrine tissues and monitor cell infiltration in the pancreatic islets (25). This approach employs mouse lymphocytes labeled with cross-linked iron oxide nanoparticles (CLIO) to enhance the T2 contrast of MR images. After adoptive transfer of the labeled cells to NOD/SCID mice, pancreatic tissues were excised and the MR images were obtained ex vivo. The investigators further applied this approach to visualize insulinitic lesions that consist predominantly of cytotoxic CD8+ T cells (33). As shown in Figure 1, the MRI contrast agent was constructed by attaching multiple copies of a synthetic peptide (NRP) that targets beta cell autoantigens to the surface of CLIO via the interaction between biotin and avidin. The images acquired in live NOD diabetic-prone mice showed that the CD8+ T cells were tracked in the pancreatic tissues (33).

Figure 1
Schematic CLIO-NRP-V7 probe. Biotinylated NRP-V7/H-2Kd complex was coupled to CLIO particles modified with avidin. CLIO-NRP-V7 probe is recognized by the TCR on NRP-V7-reactive CD8+ T-cells. (Copyright © 2007 American Diabetes Association. From ...

Superparamagnetic iron oxide nanoparticles (SPIO) have also been used to label islet transplants and longitudinally monitor their fate non-invasively. Saudek and coworkers labeled beta cell islets with commercial SPIO and transplanted them into livers of experimental rats via the portal vein (30, 39). The SPIO-labeled islets were clearly visible in the liver of both healthy and diabetic rats up to 22 weeks by MRI. It was also observed that the blood glucose levels in diabetic rats were significantly decreased after islet transplantation, indicating that the SPIO particles did not destroy the functionality of beta cell islets. They further used this method to longitudinally monitor in vivo tolerance of transplanted pancreatic islets in both syngeneic and allogeneic rat models (40). Within seven days post transplantation, the allogeneic animals exhibited similar MRI islet patterns to the animals in the syngeneic group; all animals remained normoglycemic. By day 12, all the allogeneic animals turned diabetic and the detectable transplanted islet spots on MR images became significantly fewer at 14 days post transplantation. In contrast, the syngeneic animals remained norglycemic and the number of transplanted islets detected by MRI remained relatively constant over the entire six week study period (40). This clearly shows that MRI methods using SPIO labeled islets can be used to non-invasively detect in vivo tolerance and rejection of islet transplants.

Insulin secretion from the pancreatic beta cell is a Ca2+-dependent event. Recently, Roman and coworkers reported an enhanced MR method using Mn2+ as a paramagnetic surrogate of Ca2+ to assess beta cell function in a cell culture as well as in isolated mouse islets (44). Exogeneous Mn2+ appears to be taken into beta cells via Ca2+ channels and this results in a 200% increase in contrast in T1 weighted MR images upon stimulating the cells or islets with D-glucose for insulin secretion (44).

In 2000, Balaban and coworkers reported a method to alter image contrast via chemical exchange saturation transfer (CEST) of pre-saturated slowly exchanging –NH or OH proton spins of MRI contrast agents to bulk water (50, 51). Due to the small chemical shift difference (typically < 5 ppm) between the exchanging –NH and –OH protons in diamagnetic molecules and bulk water, it is difficult to apply CEST in tissues where the bulk water resonance has broadened baseline (38). However, Sherry and others have demonstrated that in some paramagnetic lanthanide complexes, the bound water resonance is shifted as much as 800 ppm away from the bulk water resonance (38, 5266). Importantly the MR image contrast of such paramagnetic CEST agents (PARACEST) is largely determined by the chemical exchange characteristics of lanthanide complexes and to much less extent their relaxation properties (60). This has opened a novel avenue to design biologically responsive MR imaging agents. Indeed, a PARACEST agent, EuDTMA-2PB3+ (Figure 2), is able to map tissue glucose by CEST imaging (61). Physiological concentrations of glucose can be potentially quantified by using a clinical MR scanner and this europium complex.

Figure 2
CEST images of 10 mM EuDTMA-2PB in the presence of 0, 5, 10 or 20 mM glucose. The images were obtained by subtraction after a 2s presaturation pulse at either 30 or 50 ppm.

3.2. Optical Imaging Methods

Current optical imaging techniques include the well developed systems of confocal microscopy and optical coherent tomography for the studies of superficial tissues and cells, and reflectance imaging and diffuse optical tomography to image deep tissues (27). Recently a number of research groups have successfully applied these methods to study the biology and function of beta cells in the intact pancreas (27, 6770) and in transplanted islets (23, 27, 36, 43, 46, 7174). There are two chief ways of enabling optical imaging studies: (1) transfect the islets with reporter genes that produce light-emitting proteins upon external light excitation (e.g. green fluorescence protein) or enzymes that act on substrates (e.g. luciferase and luciferin) to emit visible light; (2) develop targeted molecular beacons that absorb external light of one wavelength and emit light at another wavelength with high efficiency.

To date, in vivo bioluminescence imaging (BLI) has been utilized by various groups for the assessment of pancreatic beta cell mass after islet transplantation (29, 36, 46, 71, 73). To image and quantify transplanted islets by BLI, healthy murine or human islets are transfected by adenovirus-mediated gene transfer to express luciferase prior to transplantation. As reported by Powers and coworkers, the survival of transplanted human or murine islets in NOD-SCID mice could be quantitatively assessed by BLI up to eighteen weeks (73). However, it was also reported that luciferase expression after adenovirus-mediated gene transfer is transient and attenuates ~10-fold starting from 2 days post transplantation while luminescence is relatively stable out to ten days post transplantation (75). Lentivirus has also been tested for the gene transfer. While lentivirus provided longer lasting luciferase expression than infection by adenovirus, the viral transduction efficiency of lentivirus was lower (75). It is noteworthy that Park and coworkers recently established a transgenic mouse model (MIP-luc) by introducing the mouse insulin I promoter (MIP)-luciferase transgenic construct into the pronucli of fertilized oocytes from CD-1 mice (76). The transgenic mice have normal glucose tolerance and pancreatic architecture. Importantly, luciferase expression was only observed in the pancreatic islets not in other organs. It is expected that such a transgenic animal model would be useful for the real time studies of beta cell function under different physiological conditions using in vivo BLI (76).

The available chromophores that could be used to develop molecular beacons for optical imaging have been thoroughly reviewed by Achilefu (27). Considering that the pancreas is deep within the abdomen, the chromophores that emit near infrared radiation (NIR: 700 – 900 nm) are preferred for reasons of tissue penetration. By conjugating a commercially available NIR dye, Cy5.5, with annexin V, Moore and coworkers were able to detect the difference levels of apoptosis of beta cell islets between diabetic and control animals in the animal models of both TID and T2D in vitro and ex vivo. Because annexin V is an early marker of apoptosis, such a NIR probe may enable the early detection of diabetic beta cell death (77). The same group also reported a dual modality method to non-invasively monitor transplanted human pancreatic islets under the kidney capsule of NOD-SCID mice by labeling the islets with Cy5.5 modified SPIO nanoparticles (78). However, in vivo detection was performed by MRI, while the optical imaging was used only to confirm the presence of the imaging probe in the graft and to differentiate labeled versus nonlabeled islets ex vivo.

3.3. Nuclear Imaging Methods

It has been reported that a glycogen pool exists in insulin-producing beta cells but not in acinar cells in spontaneously diabetic animals (7981). Therefore as early as in 2000, the most commonly used PET imaging probe, 18F-FDG (2-deoxy-2-18F-fluoro-D-glucose) (18F: t1/2 = 109 min), was used by Malaisse and coworkers for imaging and quantification of the endocrine pancreas in rats (82, 83). Based on the fact that the phosphorylated 18F-FDG cannot proceed further in the glycolytic pathway, an elevated accumulation in the glycogen pool was expected. Following intravenous injection, uptake of 18F-FDG in various organs of interest was examined. It was found that indeed the accumulation of 18F-FDG in the rat pancreas was three times the paired plasma value at 4 h post injection. However this elevated pancreas uptake in rats could not be reproduced in the subsequent human studies (84). Malaisse and others have resorted to other radiolabeled monosaccharides, such as D-mannoheptulose, for the selection of suitable candidates for in vivo imaging of the pancreatic beta cells (41, 8495). In rodents, uptake of tritiated D-mannoheptulose in liver and transplanted islets was found up to eight times higher than the paired value found in pancreas (96). Hence, Malaisse and coworkers designed several nuclear imaging probes based on D-mannoheptulose, such as 1-11C-labeled-D-mannoheptulose, 3-deoxy-3-18F-fluoro-D- mannoheptulose, and 7-deoxy-7-123I-iodo-D-mannoheptulose (41, 84, 87). The radiochemical preparation and in vivo evaluation of these PET/SPECT tracers have not been reported to date.

In addition to saccharide derivatives, Malaisse and coworkers also used an 125I labeled monoclonal antibody directed against rat islet beta cell plasma membrane for selective imaging of the pancreatic beta cells by SPECT (97). The radiolabeled antibody showed approximately one order of magnitude higher uptake in isolated islets than in acinar tissue but this difference was found nearly the same in the tissues obtained from control and diabetic rats, indicating that antibody uptake could not reflect a reduction in the number of beta cell islets in the diabetic pancreas. Not surprisingly, no significant difference of pancreas uptake was observed in in vivo studies performed from 1 to 4 days post injection.

Sweet and coworkers recently attempted to use another existing beta cell specific antibody (K14D10) for the assessment of pancreatic beta cell mass (98). Considering that antibody fragments usually have better blood clearance that may improve the desired pancreas contrast, they evaluated a fragment of the antibody as well. Although the fragment and the intact antibody showed similar binding affinity to beta cells (6 – 20 nM), their low binding specificity to beta cells versus exocrine cells did not warrant further in vivo evaluation.

A successful attempt of using monoclonal antibodies for beta cell imaging was reported by Moore and coworker in 2001 (99). They used the beta cell specific antibody, IC2, which had shown exclusive binding to the surface membrane of beta cells (100102). The antibody was conjugated to a bifunctional chelator, diethylenetriamine pentaacetic acid (DTPA), then labeled with 111In. Both in vitro and in vivo evaluations showed that accumulation of 111In-DTPA-IC2 was specific to beta cells. More impressively, the imaging probe uptake in the islet beta cells showed a positive correlation (r2 = 0.936) with the reduction of beta cell mass in the diabetic rats. This correlation was further confirmed by ex vivo nuclear imaging of excised organs at 24 h post intravenous injection of the 111In-labeled antibody. In spite of the promising results, the major drawback of this study is the nuclear imaging was not carried out in live animals. As the authors indicate, further work, such as modification of the probe and mechanistic studies of the antibody’s specificity, needs to be done for future practical clinical applications.

By analogy to in vivo BLI, the method of reporter gene transfer has also been applied to nuclear imaging of beta cell islets, where the reporter gene was herpes simplex virus type 1 thymidine kinase (HSV1-TK), a common suicide gene used for cancer gene therapy (103, 104). Nuclear imaging probes have been reported for non-invasively imaging HSV1-TK gene expression (105108). Among them, 18F-labeled FHBG (9-(4-18F-fluro-3-hydroxymethylbutyl)guanine) and iodine radioisotope-labeled FIAU (5-123,124,131I-iodo-2’-fluoro-2’-deoxy-1-β-D-arabinofuranosyluracil) are the most commonly used tracers (Figure 3). After intravenous injection, these nuclear imaging probes are monophosphorylated by thymidine kinase expressed in tissues transfected by the HSV1-TK gene and thereby trapped in cells and detected by nuclear imaging (107). Since other tissues also take up the imaging probe, high background emission from non-expression tissues decreases image contrast. Hence, the sensitivity of such methods is inherently lower than BLI where visible light is only emitted when the injected luciferin encounters luciferase in expressed tissues.

Figure 3
Chemical structures of 18F-FHBG and 124I-FIAU.

A nuclear reporter gene imaging approach has been reported recently for non-invasive imaging of beta cell islet grafts in NOD-SCID mice by Phelps, Kaufman, and coworkers (109). They transfected human islets with adenovirus-mediated gene transfer of a HSV1-TK mutant, HSV1-sr39tk. A CMV promoter was chosen to drive the sr39tk gene expression in islet cells rather than an insulin promoter that might be affected by blood glucose levels. The PET signal intensity of 18F-FHBG directly correlated with islet mass (r2 = 0.739, P = 0.03) as shown by analysis of PET images of human islets (1,000, 2,000, and 3,500 islets) implanted in axillary cavity of NOD-SCID mice. The diabetic mice that received 3,500 islets became euglycemic a few days after the implantation, indicating that human islet function was not significantly altered by the sr39tk gene transduction. The authors further longitudinally monitored the fate of rat islets implanted in liver by transfusing 1,500 – 2,000 islets into the mesenteric vein of diabetic NOD-SCID mice by microPET imaging with 18F-FHBG. Interesting, it was found that the background uptake of 18F-FHBG in the regions of head and chest was much higher in mice that received intrahepatic islets than in those that did not receive implants. The investigators attributed this observation to the metabolic imbalance associated with T1D and transient hyperglycemia in those animals. After subtracting the background signal, a 3-fold signal enhancement was observed in the liver region of animals that received islet implants at 4 days after transplantation in comparison with the same region of the animals without implanted islets. This signal enhancement dropped to 2-fold at 10 days after transplantation, and completely diminished at 40 days after transplantation. However, the mice remained euglycemic throughout the study period (50 days). As the imaging probe was cleared from the guts and kidneys, the microPET images reported showed spillover signals into the regions of interest. To overcome this problem, the investigators suggested using imaging probes with longer half-lives, e.g. 124I-labeled FIAU (124I: t1/2 = 4.18 d), so that imaging acquisition could be performed after the probe clears from non-target organs (109).

A number of compounds have been reported to have a specific binding affinity for beta cells such as the commonly prescribed sulfonylureas for the treatment of T2D (110). These compounds could potentially be developed as imaging probes for beta cells. However, to evaluate these compounds one by one in animal models or humans is a formidable and costly task. In light of the situation, Sweet and coworkers proposed a systematic in vitro screen method to select candidate compounds as potential beta cell imaging agents. Given the beta cell population in the pancreas, they set a criterion for potential imaging probe candidates with at least two orders of magnitude higher accumulation in beta cells versus in non-beta cells (111). For the systematic screening, they chose to use two beta cell types, INS-1 and rat islets. The former has a homogeneous cell population but the cells are not native, the latter contains not only the native beta cells but also non-beta cells in addition to diffusional tissue space. An exocrine pancreatic cell line, PANC-1, was used as a control. Two parameters were utilized to evaluate the specificity of candidate agents: cell uptake of radiolabeled candidate agents after a 30 min incubation period and radioactivity retention after a 40 min incubation period with radiolabel-free media. Eight compounds were screened using this methodology: glibenclamide, tolbutaime, serontin, L-DOPA, dopamine, nicotinamide, fluorodeoxyglucose, and fluorodithizone. Whereas fluorodithizone showed the highest uptake in both rat islets and INS-1 cells, the highest beta cell binding specificity was exhibited by glibenclamide. However, uptake of glibenclamide in islets was only about 9 times that seen in PANC-1 cells in the absence of albumin. Interestingly, the specificity of dopamine was nearly as high as glibenclamide in rat islets but it became very low in INS-1 cells due to higher levels of secretory granules found in islets compared to beta cells. This feature of the pancreatic islets provides the basis of using 18F-labeled DOPA to clinically diagnose two distinct forms of insulinism, a different beta cell abnormality, which we will discuss later. Although none of the compounds showed enough specificity to meet their preset criteria, two compounds with the highest specificity were selected for further in vivo evaluation in rats. Consistent with the authors’ prediction, neither of the two compounds showed meaningful accumulation in the pancreas. To some extent, the result validated this systematic in vitro screening methodology for establishing guidelines for other researchers’ studies.

As indicated above, a group of sulfonylureas are widely prescribed as antidiabetic agents for clinical treatment of T2D (110). They target a sulfonylurea receptor family with three known members: SUR1, SUR2A, and SUR2B. Of the three SUR receptors, SUR1 is overexpressed at the intracellular surface of the pancreatic beta cell plasma membrane but not in the exocrine pancreatic tissues (112116). Therefore two commonly used sulfonylureas, glibenclamide and tolbutamide and their derivatives have been explored to develop specific beta cell imaging probes. Glibenclamide is named as glyburide in the United States.

Based on the parent structures of glibenclamide and tolbutamide, nearly two dozens of compounds or precursors have been designed, synthesized, and radiolabeled with 18F or 11C for PET imaging of the pancreatic beta cells by collaborations among the laboratories of Shiue, Schneider, and Schirrmacher in the United States and Germany. The lipophilicity (LogP), dissociation constants (Kd), half maximal inhibitory concentrations (IC50), Hill coefficients, as well as insulin stimulation index of the new compounds have been measured and compared to those of the parent compounds (87, 117119). Based on in vitro results, two compounds, 2-18F-fluoroethoxy-5-bromoglibenclamide and 2-18F-fluoroethoxy-5-iodogliben-clamide, were evaluated in normal and diabetic mice (87) or normal rats (119). However, their accumulation in the pancreas was only marginally higher than in brain and pancreas accumulation was lower than the surrounding organs, such as kidneys, intestines, spleen, and blood (87, 119). Furthermore, most of the injected doses of both compounds ended in liver without efficient hepatic clearance out to two hours post injection. Schneider and coworkers also made the first attempt to visualize the pancreatic beta cells with 2-18F-fluoroethoxy-5-bromoglibenclamide in two healthy human subjects. Due to the approximately 10-fold higher relative uptake in the liver and slow washout from the blood, they were unable to visualize the pancreas (119). As the authors explained, the major reason for this failure could be attributed to avid binding of the compounds to plasma albumin. Indeed it was reported that nearly 99% of sulfonylureas in the blood is associated with albumin (120, 121). In light of this problem, the authors proposed to increase the hydrophilicity of these compounds to reduce high uptake and retention in liver and blood. By replacing the fluoroethoxy functional group in 2-fluoroethoxy-5-bromo- glibenclamide with 2-(bis(carboxymethyl)amino)ethoxy, they synthesized a new glibenclamide compound that can be radiolabeled with either 99mTc or rhenium radioisotopes for SPECT imaging (119). Indeed, the 99mTc-labeled compound showed a 20-fold higher hydrophilicity as compared to the parent compound. It was evaluated in normoglycemic rats and, as expected, its uptake in liver and blood was more than three orders of magnitude lower than that of 2-18F-fluoroethoxy-5-bromoglibenclamide. Although the pancreas uptake was also 10-fold lower, the contrast between the pancreas versus liver or the blood was significantly improved (119).

Repaglinide (Figure 4) is a non-sulfonylurea drug for the treatment of T2D, which also acts on SUR1. Due to its rapid in vivo kinetics and high binding affinity to SUR1, Schirrmacher and coworkers designed and synthesized two precursors in order to prepare 18F-labeled and 11C-labeled repaglinide (122, 123) as potential beta cell imaging agents. Both PET tracers showed promising results in vitro but the have not been validated as PET imaging agents for beta cells to date.

Figure 4
Chemical structures of glibenclamide, tolbutamide, and repaglinide.

The pancreas is an innervated peripheral organ with both parasympathetic and sympathetic neurons to tightly control its endocrine and exocrine functions. In fact, the pancreatic beta cells and neuroendocrine cells display many functional similarities and share a large number of gene products (124, 125). This underlines a hypothesis that the neural imaging agents may find applications in beta cell imaging.

To date three successful attempts to employ neural imaging agents for beta cell imaging have been reported. This approach was first communicated by Clark and coworkers in 2003 (26). A radioligand that binds to the presynaptic vesicular acetylcholine transporter, 4-18F-fluoro-benzyltrozamicol (FBT) (Figure 5), was used to scan four adult mice, two adult rhesus monkeys, and one adult human by PET. Impressively, the pancreas was clearly visualized in the PET images of all three mammals, which were dynamically scanned from 10 to 90 min post intravenous injection. The pancreas uptake of the PET tracer was persistently observed over the study period. While the liver was also shown in the images, the contrast measured by maximum standardized uptake values (SUV) for the pancreas versus liver was well above 1 in all scanned subjects. The mice exhibited the highest pancreas imaging contrast (mean 3.24; median: 3.02), followed by human (1.8) and rhesus monkeys (mean: 1.6; median: 1.7). It is noteworthy that all subjects in this study were normal mammals. To address the fact that the cholinergic innervation is reduced in T1D, and enhanced cholinergic activity may signal the onset of the disease (126, 127), the authors suggested that this PET imaging probe could be used for diagnosis of diabetes in early stages (26). For T2D, the authors pointed out that neuroreceptor imaging may provide a useful way of evaluating some pancreatic disorders related to the changes of autonomic neural activity. Although this preliminary study showed potential of using neuroreceptor imaging agents to non-invasively assess the functions as well as the mass of beta cell islets, further studies using control and diabetic subjects and with larger sample sizes are needed.

Figure 5
Chemical structures of 18F-FBT, 11C-DTBZ, and 18F-fluoro-L-DOPA.

As indicated before, L-DOPA (in a tritiated form) was among the compounds screened by Sweet and coworkers for potential beta cell imaging agent candidates (111). The relatively low in vitro beta cell binding specificity did not qualify this compound for further development as a PET imaging agent to assess the beta cell mass in diabetic patients. However, it was recently reported that 18F-labeled L-DOPA can be used to non-invasively assess another type of biological abnormality of the pancreatic beta cells by PET (128131), hyperinsulinism. In contrast to diabetes, hyperinsulinism is characterized by the hypersecretion of insulin which induces recurrent hypoglycemia during infancy causing severe neurological complications. Currently, a pancreatectomy must be carried out for the patients who are resistant to drug treatment (132135). Hyperinsulinism appears in either a focal or a diffuse form with clinically indistinguishable patterns (132, 135). The differential diagnosis of these two forms is of great importance because pancreatectomy procedures for the two forms are different. Currently, the diagnostic procedure is performed by pancreatic venous catheterization (PVS), which is technically difficult and invasive (136, 137). Thus, it would be of great value to have a non-invasive imaging method using 18F-fluoro-L-DOPA for accurate differential diagnosis.

The biochemical mechanism of the 18F-fluoro-L-DOPA method can be attributed to the neuroendocrine nature of the pancreatic beta cells. Upon decarboxylation by the aromatic amino decarboxylase (AADC) in the pathological foci, 18F-fluoro-L-DOPA is converted to 18F-dopamine, which in turn accumulates in the neurosecretory granules of the pancreatic neuroendocrine cells. This 18F-fluoro-L-DOPA trapping mechanism has been partially verified by blocking the AADC enzyme, which results in back diffusion of the PET tracer from the neuroendocrine cells into extracellular spaces (128). As clearly shown in Figure 6, this 18F-fluoro-L-DOPA PET method combined with MRI has been proven as an accurate and consistent diagnosis of focal and diffuse hyperinsulinism in three separate studies (128, 130, 131) involving 15, 14, and 7 human patients, respectively.

Figure 6
MRI, enhanced MRI, PET, and resultant coregistration images obtained from a patient with diffuse hyperinsulinism. Coregistration images confirm diffuse uptake of 18F-labeled-L-DOPA by the pancreas (orange arrows: pancreas; yellow arrows: kidneys). (Reprinted ...

The third successful example of using neural imaging agents for beta cell imaging employed 11C-labeled dihydrotetrabenazine (DTBZ) (Figure 5) (47, 48). Vesicular monoamine transporter type 2 (VMAT2) is expressed at dopamine nerve ends in the central nerve system (CNS) and in pancreatic beta cells but is absent in the exocrine tissues of the pancreas and many other abdominal tissues (138). Additionally, anti-VMAT2 and anti-insulin antibodies have been shown to co-localize in beta cell islets (139141). The specific binding affinity of DTBZ to the beta cell islet membrane was first evaluated by incubating tritiated DTBZ with total membrane proteins prepared from purified human islets and purified exocrine pancreas tissue. The tritiated DTBZ ligand bound exclusively to the human islet membrane but not to the exocrine pancreas (138).

The first in vivo biodistribution experiment with 11C-labeled DTBZ was performed in normal rats in 1994 (142). Although the pancreas showed the highest uptake among the harvested organs including the liver, spleen, kidney, and stomach at 15 – 60 min post injection, 11C-labeled DTBZ had not been considered for beta cell imaging until recently. In contrast, this PET tracer has been used as a specific ligand for VMAT2 in clinical PET imaging of the CNS since 1995 (143).

Recently Harris and coworkers reported longitudinal PET imaging studies with 11C-labeled DTBZ in seven BB-DP rats (47, 48). The animals were scanned three times during the study period at ages 7 weeks, 8 – 9 weeks, and 11 – 12 weeks, respectively. In the first and second scans, all animals were euglycemic. Pancreatic uptake was measured by max SUV values, which significantly dropped over time of study. The positively correlated relationship between the max SUV values and age (r2 = 0.58) was believed to reflect the progress of diabetes in the animals. The area under the curve of the intraperiotoneal serum insulin concentrations (AUC IPGTT) was used as an index of glycemic control. It was found that these index measurements significantly correlated with pancreatic uptake of 11C-labeled DTBZ by a hyperbolic function. Furthermore, using histomorphometry and RT-PCR assays, it was found that the decrease in pancreatic uptake of DTBZ over time was in agreement with loss of beta cells and the decline of VMAT2 expression levels as the disease was progressing (47, 48). However, the usefulness of this PET imaging agent has not yet been addressed in diabetic humans.

Cell membrane receptor specific monoclonal antibodies and peptides have long been used as targeting molecules for cancer diagnosis and therapy (144, 145). Compared to monoclonal antibodies, peptides have more efficient tissue penetration and rapid clearance from non-target organs, and normally are not immunogenic upon repetitive administration. Currently the problems associated with proteolytic peptide degradation can be largely overcome by using D-amino acids, sequence cyclization, and/or modification of the N- or C-terminal amino acids (144, 145). In spite of the success of using peptides for cancer, to the best of our knowledge, peptides have not been reported as imaging agents for the non-invasive assessment of beta cell islets.

By panning a random phage-displayed 20-mer peptide library on freshly isolated rat islets, the Brown laboratory recently obtained two peptide phage clones (termed as RIP1 and RIP2) that bind to islets ex vivo (146). In an in vitro binding assay using the INS-1 derived beta cell line, 832/13 (147), which displays robust glucose stimulated insulin secretion, the RIP1 phage clone displayed 8-fold higher beta cell uptake compared to the RIP2 phage, indicating that the RIP1 phage homes to beta cells while the RIP2 phage may bind to other cell types in islets. To test the in vivo beta cell binding of these phage clones, RIP1, RIP2, and a control phage clone containing a random peptide sequence were evaluated in both Sprague-Dawley rats and Zucker diabetic fatty rats (a T2D animal model) by the jugular vein injection. The phage clones were allowed to circulate in the animals for 2 h and after the animals were sacrificed, the harvested organs were stained with an anti-phage antibody to visualize the presence of phage. As shown in Figure 7, the RIP1 phage is clearly visible in rat islets and the image concurs with insulin expression stained with an anti-insulin antibody. This suggests that the RIP1 phage preferentially binds to beta cells. Impressively, the RIP1 phage did not show significant accumulation in the pancreatic islets of the T2D diabetic rat, suggesting that it can differentiate between functional and dysfunctional beta cells.

Figure 7
Distribution of RIP1 and RIP2 phage in the pancreata from Sprague-Dawley or ZDF rats. The phage was injected intravenously into the jugular vein and allowed to circulate for 2 h. Aligned sections are shown staining with anti-insulin or anti-phage antibodies. ...

To explore the potential application of the RIP1 phage clone and its targeting peptide sequence as nuclear imaging agents for non-invasive beta cell mass and/or function assessment, we have preliminary evaluated the RIP1 phage clone by radiolabeling it with 125I and with 124I (t1/2: 4.18 d; β+: 23%) for in vitro and in vivo studies. A control phage with random peptide sequence was used for comparison. Both RIP1 and control phage clones were labeled with 125I and 124I at radiochemical yields of 30 – 40%. The highest achievable specific activity was 5 × 10−5 µCi/cfu. Analyzed by radio-ITLC, greater than 95% radiochemical purity was obtained for the 125I or 124I labeled phage clones after separation and purification.

In vitro assays were performed on both freshly isolated rat islets and INS 832/13 cells. Islets were isolated from the pancreas of Sprague-Dawley rats weighing 150–175 g and embedded into alginate beads (ϕ 2.5-mm). The 125I-labeled phage clones were then added (n = 5 for each phage) and the mixture was incubated at 37°C for 30 min, after which the beads were washed three times by cold PBS (10 mM). Phage binding was determined by a gamma counter. For studies using the insulinoma cells, 1 × 107 cfu of each 125I labeled phage clone (0.4 – 0.7 µCi) was incubated with 1 × 106 INS 832/13 cells (six wells per phage) in a 12-well plate at 37°C. After 30 min, the cells were washed by cold PBS three times and imaged by a Cyclone autoradiography system (Perkin Elmer). After the imaging, the cells were harvested and counted using a gamma counter. As shown in Figure 8, the number of RIP 1 phage attached to rat islets embedded in beads was significantly higher than that of the control phage (RIP1: (3.16 ± 1.17) × 105 cfu/bead; Control: (0.95 ± 0.35) × 105 cfu/bead. p < 0.005).

Figure 8
Uptake of 125I labeled RIP1 and control phage clone in islet-embedded alginate beads (n = 5). Data are presented as mean ± s.d.

Because the pancreatic islets represent a mixture of cells, the two 125I labeled phage clones were further tested on INS 832/13 beta cells. As shown in Figure 9 (lower panel), 3-fold greater uptake of phage in the beta cells was observed for the RIP1 phage compared to the control phage. Consistent with this finding, cells incubated the RIP1 phage showed significantly higher signal intensity by autoradiography than cells incubated with control phage (Figure 9, upper panel).

Figure 9
INS 832/13 cell uptake of 125I labeled RIP1 and control phage clones. Upper panel: autoradiographic image of a 12-well plate. Left six wells: 125I labeled RIP1 phage; right six wells: 125I labeled control phage. Lower panel: Gamma counts of the INS 832/13 ...

In vivo biodistribution studies of the two 125I labeled phage clones were carried out in normal male Sprague-Dawley rats at the age of 4–5 weeks weighing 150–175 g. Each animal received 5 µCi of 125I labeled phage clone via tail vein infusion and were subsequently sacrificed at 1, 4, 24 and 48 h post injection (n = 4 at each time point). Organs of interest were removed, weighed and counted. Standards were prepared and counted along with the samples to calculate the percent injected dose per gram (%ID/g).

As shown in Figure 10, uptake of 125I-labeled RIP1 phage by the pancreas was significantly higher than that of 125I-labeled control phage at 4 h p.i. (RIP1: 0.35 ± 0.08 %ID/g; Control: 0.17 ± 0.05 %ID/g. p < 0.01). Considering the phage size, it was surprising to see low uptake of both phage clones in liver (RIP1: 1.14 ± 0.55 %ID/g; Control: 0.93 ± 0.19 %ID/g at 4 h p.i.) and rather efficient overall clearance (RIP1 and Control: > 80%ID was excreted within 24 h p.i.). Both phage clones were rapidly cleared from the blood stream (RIP1: 0.56 ± 0.05 %ID/g at 1-h p.i., 0.37 ± 0.08 %ID/g at 4-h p.i., and 0.04 ± 0.00 %ID/g at 24-h p.i.; Control: 0.34 ± 0.03 %ID/g at 1-h p.i., 0.32 ± 0.75 %ID/g at 4-h p.i., and 0.03 ± 0.01 %ID/g at 24-h p.i.). Impressively, at 4 h p.i., the RIP1 phage showed significantly lower accumulation in both the spleen (RIP1: 1.41 ± 0.29 %ID/g; Control: 5.30 ± 0.96 %ID/g. p < 0.001) and the kidneys (RIP1: 0.45 ± 0.04 %ID/g; Control: 1.21 ± 0.14 %ID/g. p < 0.001) than that of the control phage.

Figure 10
Comparative biodistribution data of 125I labeled RIP1 and control phage clones in pancreas uptake at 1, 4, 24, and 48 h p.i (n = 4). Data are presented as mean ± s.d.

Because the RIP1 phage demonstrated elevated uptake in the pancreas, lower accumulation in the spleen and the kidneys, and efficient clearance from major organs in the biodistribution studies in normal rats, we set out to image the pancreas with 124I-labeled RIP1 phage in normal rats. Sprague-Dawley rats were injected with the two 124I-labeled phage clones via the tail vein (640 – 683 µCi of 1 × 109 cfu) and imaged using a home-built small animal PET system (148) at 4 h p.i. As shown in Figure 11, with 124I-labeled RIP1 phage, a bright area between the stomach and the liver is clearly visible. However, limited by the sensitivity of our small animal PET system and the capability of our in-house developed image reconstruction software (148, 149), we could not identify with certainty whether the intense areas reflect the pancreas or other abdominal organs. To answer this question definitely we performed a post-PET biodistribution study of rats after imaging. The ratios between the uptake values (%ID/g) of the 124I-labeled RIP1 phage in the pancreas and other organs are 16.2 (pancreas/brain), 6.3 (pancreas/fat), 5.9 (pancreas/muscle), 1.4 (pancreas/kidney), 1.3 (pancreas/liver), 0.6 (pancreas/stomach), and 0.3 (pancreas/spleen). Therefore, the bright region between the stomach and the liver in Figure 11 very likely reflects the pancreas. Further evaluations of this RIP1 phage are under investigation.

Figure 11
PET imaging with 124I-labeled RIP1 phage in a healthy Sprague-Dawley rat (183 g) at 4 h p.i. Coronal image slices (1-mm thick) from posterior (z = 45) to anterior (z = 56).

Taken together, our preliminary data show that the RIP1 phage preferentially accumulates in the pancreas. Considering a previous report on this phage (146), we conclude that the elevated pancreas uptake of the 125/124I labeled RIP1 phage is likely caused by its specific beta cell binding. The 125/124I labeled RIP1 phage clones also showed high uptake in the stomach. This is likely due to the endogenous sodium iodide symporter (NIS) expression in the stomach which absorbs an extra amount of 125/124I radioactivity in the form of free iodide because of the deiodination of the radiolabeled phage.

Although both phage clones showed relatively efficient clearance from the animals, they have inherently tendency to accumulate in the organs of the reticuloendothelial system (RES), such as the liver and spleen, simply due to the phage particle size. Considering these factors, we plan to use the RIP1 peptide sequence for the further development of beta cell imaging agents. The Brown laboratory has recently designed and reported a unique scaffold constructed from a branched lysine core to present multiple copies of targeting peptides on the end of polyethylene glycol (PEG) chains (150156). For cell-specific delivery of payloads, such as drug, imaging probes, and genes, a cysteine handle is introduced to the construct for payload attachment. In fact, the design of such a scaffold was partially intended to mimic the multimeric fashion of the peptides presented on the tip of the M13 phage clones in phage display. A typical tetrameric peptide construct is shown in Figure 12.

Figure 12
A typical construct for a tetrameric peptide.

To avoid excess stomach uptake seen in the radioiodine experiments, this radioisotope will be avoided in future radiochemistry procedures. To date, we have designed and synthesized several maleimide derivatives as precursors to radiolabel the cysteine-containing peptide constructs with 18F, 64Cu, 99mTc, or 111In for PET and SPECT imaging of the pancreatic beta cells.

4. CONCLUSIONS

In summary, there is a growing need to develop early diagnostic methods for the non-invasive assessment of the pancreatic beta cells as T1D and T2D and other beta cell associated metabolic diseases are becoming epidemic. Newly developed imaging agents will aid in the mechanistic understanding of the progression of beta cell disease as well as being translated into the clinic for early diagnosis. Among the current imaging methods, MRI provides images with the highest resolution. Aided by SPIO as a T2 contrast agent, MRI has been successfully applied to monitor the mass change of transplanted beta cell islets for the treatment of T1D. Other alternative ways, such as using responsive Mn-enhanced or PARACEST MRI contrast agents, have also shown potential in the assessment of the pancreatic beta cells. Due to insufficient deep tissue penetration, optical imaging techniques are currently confined to small animal studies although BLI has shown promising results for non-invasive assessment of the fate of transplanted pancreatic islets. Successful PET imaging of the normal pancreas in three mammalian species with 18F-labeled FBT, the diabetic pancreas in rats with 11C-labeled DTBZ, and the clinical differentiation of focal and diffuse hyperinsulinism with 18F-labeled L-DOPA, nuclear imaging methods have great momentum to move forward the molecular imaging of the pancreatic beta cell islets.

With the superior inherent sensitivity, the role of nuclear imaging techniques is mainly defined by the successful development of radiotracers that can specifically target the pancreatic beta cells. Based on the neuroendocrine nature of the pancreatic beta cell islets, it appears straightforward to systematically screen the current existing neuroimaging agents for such beta cell islet specific nuclear imaging probes. In addition, our preliminary data have shown that peptide sequences selected by panning random phage-displayed peptide libraries on freshly isolated islets also have potential.

Supplementary Material

Publisher note

ACKNOWLEDGEMENTS

This work was partially supported by a Program Project Grant from the National Institutes of Health (PO1 DK058398).

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