Ionic liquids for oral insulin delivery

Significance

Abstract

The oral route of drug administration is preferred over injections due to its ease of administration, high patient compliance, and low manufacturing costs. However, due to various gastrointestinal barriers to drug absorption, it is unsuitable for the delivery of biologics. For example, insulin is an indispensable medication for type 1 diabetes management. It is currently administered as an s.c. injection but is associated with lack of patient adherence due to pain and needle phobia associated with injections (1). Orally delivered insulin could significantly enhance patient compliance. In addition, it would closely mimic the physiological path of pancreatic insulin (2, 3). Oral/pancreatic insulin is transported to the liver via the portal vein where 80% is retained and the rest reaches systemic circulation, creating up to threefold higher insulin concentration in the portal vein compared with systemic circulation (3). This portal-peripheral insulin gradient is disrupted when insulin is injected s.c. due to a higher systemic insulin concentration compared with that in the portal vein (only ∼20%) which disrupts the liver’s fine balance between glycogen storage and glucose output. This often results in hyperglycemia, which, when treated with higher insulin dose, can lead to hypoglycemia (3, 4).

The pursuit of an oral insulin product began many decades ago. Several strategies have been developed to overcome the gastrointestinal barriers to oral absorption of biologics. However, no formulation has successfully cleared all clinical hurdles, and therefore, no oral insulin products are commercially available. Products that have completed or are currently in phase II clinical trials include enterically coated capsules with additives to improve oral insulin uptake (Capsulin by Diabetology Ltd and ORMD-0801 by Oramed Ltd), hepatic directed liposomal insulin (HDV-Insulin by Diasome Pharmaceuticals Inc.), polyethylene glycol (PEG) conjugated insulin (IN-105 by Biocon Ltd.), insulin-proinsulin-c-peptide in Oshadi carrier (Oshadli Icp by Oshadi Drug Administration Ltd), and long-acting insulin analog tablets using gastrointestinal permeation enhancer technology (GIPET 1 by Novo Nordisk) (5–7). Active recruitment of participants for safety and efficacy studies is currently underway only for ORMD-0801 and Oshadi Icp, according to the clinicaltrials.gov list. In addition, many products require multistep formulation procedures, various additives, or chemical modification of the protein, which have their own shortcomings. With the emerging global diabetes epidemic, there is a sense of urgency to develop safe, effective, and easily scalable oral insulin products.

We have developed an ionic liquid (IL)-based oral formulation of insulin and determined its safety, efficacy, and long-term stability. Ionic liquids consist of organic/inorganic salts with melting points below 100 °C and have been widely used in various novel chemical and pharmaceutical technologies (8–10). In the present work, we utilized a room temperature stable choline and geranate (CAGE) deep eutectic solvent that had earlier demonstrated remarkable efficacy in transdermal delivery of antibiotics and insulin (11, 12). Insulin was dispersed in CAGE in a single-step process, and its safety and efficacy was evaluated both in vitro and in vivo as well as its storage stability. The study demonstrates an unprecedented improvement in oral bioavailability of insulin with excellent oral efficacy, biocompatibility, and long-term stability.

Results

Insulin Was Stable in CAGE for Long Periods of Time.

Insulin has an inherent alpha-helical conformation, which is essential for its receptor interaction and hence its bioactivity (13). Before performing functional tests of oral delivery with CAGE, we assessed whether insulin is stable in CAGE for extended periods of time. We stored insulin-CAGE at room temperature (RT, away from direct sunlight) or under refrigeration at 4 °C and evaluated the secondary structure of insulin isolated from CAGE every month for a period of 4 mo using circular dichroism (CD). Results showed the presence of double negative troughs at around 207 and 222 nm, which is a typical representation of an alpha-helix in a CD graph (Fig. 1). No difference in the shape or degree of ellipticity was noticed between freshly prepared insulin solution and insulin stored in CAGE at RT or 4 °C for up to 3 and 4 mo, respectively. The result suggests that CAGE preserves the secondary structure of insulin for long periods of time.

Open in a separate window

Fig. 1.

Circular dichroism spectra of insulin isolated from CAGE at different months. Insulin was dispersed in CAGE and stored at RT (25 °C) or under refrigeration at 4 °C for up to 4 mo. The alpha-helical secondary conformation of insulin was retained in CAGE for extended periods of time.

To validate the CD stability data, we evaluated the biological activity of insulin isolated from CAGE at different times in nondiabetic rats. For this purpose, rats that were fasted overnight were s.c. injected with insulin (isolated from CAGE and resuspended in sterile saline), and blood glucose was monitored for a period of 8 h. No significant difference in biological activity was seen between fresh insulin and insulin-CAGE stored at RT for 1–2 mo or at 4 °C for 1–4 mo (SI Appendix, Fig. S1). An attenuated efficacy was observed for insulin stored at RT for 3 mo, whereas insulin stored at 4 °C with CAGE did not show any loss in bioactivity even after 4 mo of storage. This clearly illustrates that CAGE is an excellent solvent for long-term storage of insulin.

Insulin-CAGE Caused Profound Hypoglycemia and Demonstrated Exemplary Pharmacokinetics upon Intrajejunal Administration.

To gauge the efficacy of insulin-CAGE in lowering blood glucose levels, 3–5 U/kg insulin was dispersed in CAGE and administered to anesthetized nondiabetic rats intrajejunally, followed by blood glucose monitoring every 0.5 h for a total of 5 h (Fig. 2). Rats administered with 3 U/kg insulin-CAGE showed a steady drop in blood glucose levels from 0.5 h till it dropped by 45% of its initial value (55 ± 6%) in 2.5 h. Beyond this point, the blood glucose levels plateaued, ending at 47% in 5 h. The group treated with 5 U/kg insulin-CAGE showed a sharp decrease in blood glucose levels that culminated in an ∼65% drop within 1.5 and 2 h (37 ± 5 and 35 ± 5% of initial levels, respectively). Blood glucose increased thereafter, which is a typical homeostatic response in nondiabetic rats that are subjected to a sudden and rapid decrease in blood glucose levels. At the end of 5 h, the blood glucose level was 74% of initial levels. The rats that were s.c. injected with 2 U/kg insulin also showed a similar pattern of blood glucose drop but to a lesser extent compared with 5 U/kg insulin-CAGE. A maximum drop of 51% was observed in 1 h (49 ± 8% of initial level), which rapidly recovered to 100% at the end of the study at 5 h (101 ± 7%). Controls such as neat CAGE, saline, or 3 U/kg insulin–saline intrajejunal administration did not bring about a significant drop in blood glucose. In all these control groups, blood glucose decreased slowly (most likely due to continued fasting) by about 25% of initial levels in 5 h.

Open in a separate window

Fig. 2.

Efficacy of insulin-CAGE in lowering blood glucose levels upon intrajejunal administration in nondiabetic rats. (A) Blood glucose lowering efficacy of various formulations compared with initial levels. (B) Blood glucose changes after normalizing for fasting effect related blood glucose changes. Animals injected with saline alone were considered as the fasting group, and data were plotted after subtracting the blood glucose obtained from the saline group. All data are represented as mean ± SE (n = 6). A significantly higher (P < 0.05) efficacy was noted in the efficacy of 5 U/kg insulin-CAGE–treated rats at various time points of the study compared with s.c. administered 2 U/kg insulin (represented by asterisks).

The pharmacokinetics of insulin absorption and elimination was determined by measuring serum insulin levels at different time points (Fig. 3). Insulin concentration rapidly increased within an hour after s.c. (SQ in figures) injection of 2 U/kg insulin and intrajejunal (IJ) administration of 5 U/kg insulin-CAGE and subsequently dropped to follow a similar pattern in elimination. The pharmacokinetic parameters calculated using serum insulin concentrations showed that the elimination half-life of intrajejunally administered insulin-CAGE was almost twofold higher than s.c. insulin (Table 1). The oral bioavailability of 5 U/kg IJ Insulin-CAGE thus calculated was found to be 51% relative to 2 U/kg s.c. injection. The pharmacodynamic bioavailability of the formulation as calculated from efficacy plots was 66% relative to 2 U/kg s.c. injection. On the contrary, 5 U/kg insulin-saline administered IJ did not show any increase in insulin level with time.

Open in a separate window

Fig. 3.

Efficacy of CAGE in enhancing the oral bioavailability of insulin. Data are represented as mean ± SE (n = 4).

Table 1.

Pharmacokinetic parameters of insulin-CAGE given intrajejunally and insulin solution administered s.c

Formulation	Kel, h−1	t1/2, h	AUCtotal, μIU h/mL	% F
Insulin-CAGE IJ	0.32	2.2	300.6	51
Insulin s.c.	0.58	1.2	237.6

Open in a separate window

Elimination rate constant (K_el), half-life (t^1/2), area under curve (AUC), and bioavailability relative to s.c. injection (F).

Insulin-CAGE Administered Orally in Capsules Demonstrated Notable Efficacy in Lowering Blood Glucose Levels.

The remarkable efficacy of CAGE in enhancing oral bioavailability of insulin upon intrajejunal administration prompted us to investigate its efficacy upon oral delivery using capsules. To this end, we placed 10 U/kg insulin-CAGE or its controls in enterically coated elongated size 9 capsules as illustrated in SI Appendix, Fig. S2, and administered them to nondiabetic rats using an oral gavage.

The group treated with 10 U/kg insulin-CAGE demonstrated a rapid 38% drop in blood glucose levels within 2 h post-capsule administration (62 ± 2% of initial level) (Fig. 4). Beyond this point, blood glucose dropped slowly but steadily by around 45% at 10 h (55 ± 3%). In comparison, s.c. administration of 2 U/kg insulin led to a sharp 49% drop in blood glucose levels (51 ± 5%) in 1 h, which rose steadily and subsequently peaked at 88% of the initial value in 4 h. Thereafter, blood glucose levels dropped in a pattern similar to formulation controls of neat CAGE, empty capsules, and insulin–saline. As earlier observed with IJ administration, insulin-CAGE in capsules demonstrated significantly sustained efficacy till the end of study, unlike s.c. insulin. To assess whether CAGE is acting solely as a permeation enhancer, we administered rats with neat CAGE in capsules followed by 10 U/kg insulin powder in capsules after a 0.5-h delay (SI Appendix, Fig. S3). A significant difference in efficacy between insulin-CAGE coadministration and consecutive administration was observed in the first few hours of the study (compare SI Appendix, Fig. S3, and Fig. 4), whereas no significant difference between insulin solution (no CAGE) and consecutive dosing of insulin and CAGE was observed through all time points (SI Appendix, Fig. S3). The study further suggests that insulin and CAGE need to be delivered together to obtain significant efficacy.

Open in a separate window

Fig. 4.

In vivo efficacy of insulin-CAGE orally administered in capsules. (A) Blood glucose lowering efficacy of various formulations compared with initial levels. (B) Blood glucose changes after normalizing for fasting effect related blood glucose changes. Animals administered with empty capsules were considered as the fasting group, and data were plotted after subtracting blood glucose changes obtained from the empty capsule group. All data are represented as mean ± SE (n = 6). A significantly higher (P < 0.05) efficacy of CAGE-insulin was observed at various time points (represented as asterisks) compared with s.c. administered insulin.

CAGE Demonstrated Good Oral Biocompatibility in Vivo.

Histological examination of small intestine samples collected 5 h after intrajejunal administration, 12 h after oral capsule dosing, or after 7 d of once-a-day repeat oral dosing showed no remarkable difference in morphology between CAGE and saline-treated animals/insulin-treated animals (Fig. 5 and SI Appendix, Fig. S4). Additionally, no significant structural damage to the small intestine tissues was noted. Particularly, fingerlike villi were found in all of the tissues. The results clearly showcase the excellent biocompatibility of CAGE with intestinal tissue, thereby validating the suitability of the formulation for oral administration.

Open in a separate window

Fig. 5.

Photomicrographs of Hematoxylin and Eosin staining of small intestine tissue sections after intrajejunal administration of (Left) neat CAGE or (Right) saline. (Scale bar: 200 μm.) (Insets) Sections at higher magnification. (Scale bar: 50 μm.)

Discussion

Over the last few decades, the prevalence of diabetes mellitus has grown so steadily that it is now being referred to as the “epidemic of the century” (14). Current recommendations for management of the disease include insulin therapy alone or in combination with oral hypoglycemics such as metformin (15). Individuals on insulin therapy alone often require either administration of intermediate-acting insulin two times a day or long-acting insulin once a day (15). Insulin is not available in the clinic as an oral pill and is almost exclusively administered as an s.c. injection. However, despite its effectiveness in the management of hyperglycemia and mitigating risks of neuropathy, nephropathy, and retinopathy, injectable insulin has lower patient compliance due to pain, interference with daily activities, and reluctance of use in public, resulting in intentional omission and poor long-term glycemic control in as much as 60% of patients (5, 16). This leads to higher hemoglobin A1C levels and increased hospitalization due to diabetes-associated complications (16). Given the rapid growth and magnitude of diabetes, it is imperative to develop an insulin therapy that would appeal to patients and avoid formulation-based adverse effects.

Oral delivery enjoys a high patient compliance but is not suitable for delivery of biologics. This is due to the fact that orally delivered drugs need to traverse through the acidic environment of the stomach which can degrade protein/peptide drugs. This can be avoided by encapsulating them in enteric or other protective coated systems. However, upon release in the intestine from their protective casings, peptide/protein drugs are exposed to the proteolytic milieu of the intestine where they are easily cleaved into smaller amino acid units by resident enzymes. If a proportion of the drug escapes proteolysis, its absorption through the intestinal mucus layer and enterocytes into the systemic circulation as an intact molecule is challenging. Oral insulin absorption is further impeded due to erratic GI transit time and lack of specific insulin uptake mechanisms in the intestine (17). A perturbation in insulin structure during GI transit may lead to significant denaturation and loss in biological activity. Therefore, not surprisingly, protein and peptide drugs have a negligible oral bioavailability of less than 1%, a stark divergence from injectable formulations where 100% of the dose is available for pharmacological activity (18). Several researchers have attempted to resolve the perennial problem of low oral bioavailability of insulin by modifying insulin; encapsulating it in novel carriers; or employing enteric coatings, absorption enhancers, or proteolytic inhibitors. Some examples include use of poly[lactic-coglycolic acid] (PLGA) or chitosan-based nanoparticles for oral insulin delivery. Pan et al. obtained a pharmacological bioavailability of 10.3% using 10 U/kg insulin loaded in PLGA nanoparticles and 15.3% using 21 U/kg insulin in chitosan nanoparticles, whereas Cui et al. obtained an oral bioavailability of 3.7 and 6.3% using 20 U/kg insulin placed in PLGA and PLGA-55 nanoparticles, respectively (19–21). Sarmento et al. (22) used chitosan–dextran nanoparticles to encapsulate insulin and observed a pharmacological bioavailability of 5.6 and 3.4% after placing 50 and 100 U/kg insulin, respectively, in the particles. Zhang et al. (23) encapsulated 50 U/kg insulin in solid lipid nanoparticles (SLN) and wheat germ agglutinin-modified SLN and obtained pharmacological bioavailabilities of 4.5 and 6.1%, respectively. Other strategies of improving oral delivery of proteins involve using proteolytic enzyme inhibitors such as sodium glycocholate, aprotinin, soybean trypsin inhibitor, bacitracin, and camostat mesilitate (24). Chemical modifications of insulin such as attaching a targeting ligand like transferrin or cell-penetrating peptides like TAT peptide have shown to assist transcytosis of insulin across enterocytes (25, 26). Absorption enhancers include bile salts, surfactants, fatty acids, calcium ion chelating agents, certain polymers such as chitosan/thiolated chitosan, and zonula occluden toxins that operate by either modulation of the cell membrane structure of intestinal epithelium for transcellular uptake or tight junction permeability for paracellular transport (24).

Recently, ionic liquids have garnered immense interest as a class of polar organic solvents for delivery of small- and large-molecule therapeutics. ILs constitute a group of salts with an organic cation and organic/inorganic anion that are typically liquid below 100 °C (27). By pairing different ions, ILs can be tailored to have different physicochemical properties such as viscosity, hydrophobicity, solubility, and biodegradability for a wide range of pharmaceutical applications in the fields of biocatalysis, enzymatic processes, protein stability, permeation enhancement, and solubilization, among others (11, 12, 27–31). In oral drug delivery, ILs have been utilized for the delivery of poorly water-soluble small molecules such as danazol, itraconazole, cinnarizine, and halofantrine (32, 33). When administered to rats orally, the plasma concentrations of the drugs in IL systems were severalfold higher compared with same dose physical mixtures or suspensions and demonstrated prolonged exposure.

Both choline and geranic acid are recognized by the Food and Drug Administration as generally regarded as safe (GRAS) ingredients. Choline, an important constituent of lecithin that is present in both plants and animals and required for various physiological functions, has an oral lethal dose 50% (LD₅₀) of 3,400 mg/kg, whereas geranic acid, commonly used as a flavoring agent in foods, has an oral LD₅₀ of 3,700 mg/kg in rats (34, 35). In this study, the oral capsule CAGE dose after single administration was 80 mg (80 μL), which comprises ∼27 mg choline and 53 mg geranic acid. Therefore, we administered a much lower dose than the oral LD₅₀ of individual constituents. An adequate choline intake is considered to be 550 mg in men and 425 mg in women per day (36). On the other hand, geranic acid is a common food additive and found in cardamom, lemongrass, petitgrain, and other essential oils (37).

Interactions of CAGE with Caco-2 monolayers were studied in vitro. CAGE exhibited concentration-dependent cellular viability in Caco-2 cells (SI Appendix, Fig. S5). CAGE also exhibited concentration-dependent enhancement of insulin transport, with the enhancement of greater than 10-fold for 50 mM CAGE (SI Appendix, Figs. S6 and S7). The enhancement mechanism is likely mediated by the paracellular route. This was further evaluated using paracellular permeability markers Lucifer yellow and fluorescein isothiocyanate (FITC)-dextran (38). The transport of Lucifer yellow also exhibited a concentration-dependent enhancement with CAGE (SI Appendix, Fig. S8). Furthermore, transport of 4 kDa FITC-dextran (comparable size to insulin) was also increased in a concentration-dependent manner, reaching an enhancement of 13-fold (SI Appendix, Fig. S9). This was corroborated by measuring the intestinal tight junction integrity through determination of transepithelial electrical resistance (TEER). As observed earlier, a concentration-dependent decrease in TEER was observed upon exposure to CAGE for 5 h, followed by concentration-dependent recovery (SI Appendix, Fig. S10). Treatment of cells with 10 mM CAGE resulted in significant decrease in TEER at 1 and 5 h, whereas treatment with 25 and 50 mM CAGE led to a significant (40–50%) decrease in TEER at all time points and TEER recovery to 90 and 58% of initial levels within 24 h, respectively. For reference, drop in TEER after exposure to a well-known permeation enhancer drug sodium caprate was also measured (39). The transcellular permeability of coumarin-6 (a fluorescent marker for passive transcytosis) in the presence of CAGE was thereafter assessed (40). Surprisingly, CAGE reduced the transcellular uptake of coumarin-6 even at low concentrations, thus suggesting that transcytosis of drugs across intestinal epithelia is unlikely to explain the observed transport enhancement for insulin (SI Appendix, Fig. S11). In addition to enhancement in paracellular permeability, CAGE significantly hindered tryptic digestion of insulin from 1 h onward till the end of study at 24 h compared with buffer control (SI Appendix, Fig. S12). CAGE was also found to significantly decrease viscosity of mucin hydrogel at 1 and 5% wt/vol concentrations (SI Appendix, Fig. S13), suggesting that CAGE likely assists in mucus penetration in vivo, a key barrier in oral uptake of macromolecules.

In vivo, CAGE demonstrated outstanding efficacy in enhancing oral uptake of insulin when administered either intrajejunally or in capsules. Intrajejunally injected 3 U/kg insulin-CAGE led to a 47% drop in blood glucose levels in 5 h, which was comparable to the drop observed with s.c. injected 2 U/kg insulin. Using 5 U/kg insulin-CAGE, an even more drastic 65% drop in blood glucose levels was observed in 2 h, and levels remained significantly lower compared with s.c. injected insulin for the remaining period of study. This is one of the lowest oral insulin doses that we have seen in the literature demonstrating such remarkable efficacy. Among other notable work, Pan et al. (20) demonstrated a 52% drop in blood glucose levels in 4 h upon oral administration of 10 U/kg insulin in PLGA particles. Using vitamin B12-conjugated dextran nanoparticles loaded with 20 U/kg insulin, Chalasani et al. (41) obtained a 70–75% drop in blood glucose and an oral bioavailability of 29.4%. Intrajejunal administration of 10 U/kg insulin in dogs using bile salt mixed micelles exhibited an absolute bioavailability of 1.8% (42). Intrajejunal placement of rectangular mucoadhesive patches loaded with 50 U/kg insulin in rats led to a relative bioavailability of 3.9%. In the presence of permeation enhancer drug dimethyl palmitoyl ammonio propanesulfonate, the relative bioavailability increased to 7.7% (43). Yin et al. (44) showed that intestinal injection of trimethyl chitosan-cysteine conjugate nanoparticles encapsulating 50 U/kg insulin decreased blood glucose levels in rats by 70%. Using Labrasol, Takada and coworkers observed bioavailabilities of 0.25 and 0.2% for intraileum and intracolonic administrations, respectively (45). An intragastric delivery of lecithin-based microemulsion containing 200 IU/kg resulted in a bioavailability of 0.148 (without aprotinin) and 0.159 (with aprotinin) in normal rats (46).

In our study, a high jejunal bioavailability of insulin was obtained. It is also to be noted that elimination half-life of the insulin-CAGE was almost twofold higher than s.c. injected insulin, indicating a more sustained efficacy. To validate the significant efficacy observed thus far, we further encapsulated insulin-CAGE in enterically coated capsules and orally administered it to rats. Enteric coating prevents breakdown of capsules in the acidic environment of the stomach and releases encapsulated material only in the more alkaline environment of the small intestine (47). Bypassing the stomach using enteric coating technology therefore prevents degradation of biologics by gastric acids. To account for dose dilution upon release of insulin-CAGE in the intestine, we used a higher insulin dose (10 U/kg) than that used in the IJ delivery. Again, insulin-CAGE produced a similar extent of blood glucose drop compared with s.c. injected insulin. However, unlike s.c. insulin, the effectiveness of insulin-CAGE was sustained till the end of study at 12 h, demonstrating the potential for its development into a long-acting oral insulin formulation. Administration of neat CAGE followed by insulin after 0.5 h did not result in any significant blood glucose-lowering efficacy (SI Appendix, Fig. S3). This indicates that coadministration of insulin and CAGE is required for achieving significant in vivo efficacy.

Ionic liquids interact with various hydrophilic and hydrophobic amino acids of a protein through an intricate balance of hydrogen bonds, disulfide bridges, hydrophobic effects, and ionic interactions (48). When mixed with other liquids such as water, a more complex interplay between ions occurs that, depending on the nature of ions, can result in formation of micelles or microemulsions (48). A prolonged and higher oral plasma concentration of poorly water-soluble drugs dispersed in ILs was also reported by Williams et al. (32). This was described to be due to improved interaction of IL-based formulations with endogenous bile salt micelles that resulted in generation of dispersed systems with better access to the intestinal absorptive surface (32). In addition, IL-based systems were found to have high drug loading and were “insensitive to gastrointestinal digestive processes” (27). CAGE also prevents enzymatic degradation, likely by limiting the access of intestinal enzymes to loaded insulin by forming a physical barrier and tempering their proteolytic activity. Enzyme activity is also modulated by its surrounding environment, and molecular dynamics simulation studies have shown that ILs can remove water from the surface of enzymes to the same extent as polar organic solvents like acetonitrile (49). Based on this information and our mechanistic studies, we believe that CAGE protects the insulin from enzymatic degradation, assists in its transport across the mucus layer, and mediates paracellular uptake through the opening of tight junctions. The high oral delivery efficacy of CAGE may be attributed to synergism between its ability to enhance permeation through the paracellular route, inhibit proteolytic enzymes, and penetrate through the mucus layer.

In addition to high efficacy, CAGE exhibited biocompatibility and long-term stability for potential application in the clinic (Fig. 5 and SI Appendix, Fig. S4). For safety determination in vivo, we isolated small intestine sections of rats treated with neat CAGE or insulin-CAGE either after single dose or once-a-day repeat dose administration for a week and found that there was no toxicity at the morphological level after intrajejunal or oral administration, demonstrating excellent oral tolerability of CAGE in vivo. However, chronic or subchronic toxicity of oral CAGE needs to be thoroughly examined.

Insulin-CAGE was stable at RT for 2 mo and at 4 °C for at least 4 mo as assessed through secondary structure and in vivo bioactivity evaluation (Fig. 1 and SI Appendix, Fig. S1). Physicochemical degradation of insulin occurs primarily due to hydrolysis, aggregation, and intermolecular transformation reactions leading to loss of potency (50). Ionic liquids can prevent interaction of proteins with water molecules, whereas protic ionic liquids have been reported to stabilize several amino acids as well as insulin’s native conformation and mitigate its self-aggregation propensity (49, 51). We believe that storage of insulin with neat CAGE prevented interaction of the protein with water, mitigating hydrolytic interaction and stabilizing its alpha-helical secondary structure. Given that the monomeric form of insulin is the bioactive form, the enhanced oral bioactivity of insulin in CAGE may also be partly attributed to presentation of insulin molecules to intestinal cells and systemic circulation as monomers.

Overall, this study outlines the development of a highly effective oral insulin formulation that has tremendous potential for clinical translation in the future. Insulin-CAGE can be prepared effortlessly in a single-step process and therefore can be easily scaled up for industrial production. The product does not require modification in insulin structure or development of complex nanostructures and therefore precludes generation of immunological reactions to modified protein or loss of active ingredient during multistep formulation development. Moreover, it is a simple and robust formulation comprising only insulin and an ionic liquid made of GRAS ingredients that eliminates the necessity to use further additives to enhance efficacy. The formulation demonstrated profound efficacy in vivo at very low insulin doses. By delivering insulin-CAGE in enterically coated capsules, we evade gastric degradation of insulin and enhance its intestinal permeability, thereby overcoming the barriers of oral delivery of biologics. Furthermore, the formulation is biocompatible and has good long-term stability. Outcomes of this study may facilitate realization of oral insulin delivery in the clinic. To this end, additional preclinical studies for chronic and subchronic tolerability, effect of food in the intestine, and efficacy in diabetic rats as well as in larger animals should be performed in the future. In addition, studies to further understand insulin-CAGE–intestinal fluid interactions should also be conducted.

Methods

Materials used for the study and preparation of insulin-CAGE are provided in SI Appendix.

Supplementary Material

Acknowledgments

Footnotes

References