Open Access Article
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Hydrophobic ion pairing: encapsulating small molecules, peptides, and proteins into nanocarriers

Kurt D. Ristroph and Robert K. Prud'homme*
Department of Chemical and Biological Engineering, Princeton University, Princeton, New Jersey 08544, USA. E-mail: prudhomm@princeton.edu

Received 16th May 2019 , Accepted 18th September 2019

First published on 1st October 2019


Hydrophobic ion pairing has emerged as a method to modulate the solubility of charged hydrophilic molecules ranging in class from small molecules to large enzymes. Charged hydrophilic molecules are ionically paired with oppositely-charged molecules that include hydrophobic moieties; the resulting uncharged complex is water-insoluble and will precipitate in aqueous media. Here we review one of the most prominent applications of hydrophobic ion pairing: efficient encapsulation of charged hydrophilic molecules into nano-scale delivery vehicles – nanoparticles or nanocarriers. Hydrophobic complexes are formed and then encapsulated using techniques developed for poorly-water-soluble therapeutics. With this approach, researchers have reported encapsulation efficiencies up to 100% and drug loadings up to 30%. This review covers the fundamentals of hydrophobic ion pairing, including nomenclature, drug eligibility for the technique, commonly-used counterions, and drug release of encapsulated ion paired complexes. We then focus on nanoformulation techniques used in concert with hydrophobic ion pairing and note strengths and weaknesses specific to each. The penultimate section bridges hydrophobic ion pairing with the related fields of polyelectrolyte coacervation and polyelectrolyte-surfactant complexation. We then discuss the state of the art and anticipated future challenges. The review ends with comprehensive tables of reported hydrophobic ion pairing and encapsulation from the literature.


1. Introduction, overview, and terminology

In the twenty years since Meyer and Manning's classic 1998 review,1 hydrophobic ion pairing (HIP) has gained prominence as a useful strategy for making charged hydrophilic molecules into hydrophobic complexes. The technique has a number of applications and has been used, among others, to dissolve molecules in supercritical CO2,2 dissolve enzymes in organic solvents without losing activity,3 improve intestinal adsorption4–6 or skin permeation,7,8 or otherwise enhance bioavailability.9

This review will focus on one of the most prevalent uses of hydrophobic ion pairing: the complexation and encapsulation of charged hydrophilic small molecule, peptide, or protein therapeutics into drug delivery vehicles. The first section summarizes the general rules for hydrophobic ion pairing. We discuss drug eligibility and class-specific considerations, review commonly-used counterions, and outline key parameters such as counterion pKa. The third section focuses on formulation techniques that have been used to encapsulate hydrophobic complexes into nanoparticles, microparticles, and emulsions for drug delivery. The fourth section discusses how ion paired drug payloads are released from their delivery vehicles. The fifth section bridges the HIP technique with polyelectrolyte–polyelectrolyte complexation (‘coacervation’) and polyelectrolyte–surfactant complexation, related fields that have remained largely unconnected from the hydrophobic ion pairing literature. We do not review another related field, nucleotide complexation with cationic lipids to form lipoplexes or solid lipid nanoparticles, but provide references to a number of excellent reviews. At the end of the article we present tables to organize the reported results of hydrophobic ion pairing used for encapsulation. The tables are sorted by both therapeutic and counterion for easy reference and rapid comparison (Fig. 1).


image file: c9na00308h-f1.tif
Fig. 1 Hydrophobic ion pairing schematic. (A) Possible charged groups (left) and hydrophobic moieties (right) for a counterion. (B) Stoichiometric ion pairing between a cationic API (blue) and anionic counterion. (C) Non-stoichiometric ion pairing. (D) Reversible ion pairing due to inadequate binding or hydrophobicity.

Hydrophobic ion pairing is the process of forming ionic interactions10 between a charged hydrophilic molecule with an oppositely-charged counterion.1 The counterion contains at least one hydrophobic domain such as an alkyl tail or aromatic ring. The complexation increases hydrophobicity by two main mechanisms: first, the molecule's natural charge is masked, mitigating solubility in polar solvents such as water. Second, the hydrophobic groups on the counterion, typically nonpolar aliphatic tails or aromatic groups, help to coat the original molecule's surface area with hydrophobic domains that exclude water.

For our purposes, the charged hydrophilic is a drug or dye and may be referred to as an ‘active pharmaceutical ingredient (API)’ or ‘therapeutic.’ The counterion is referred to in the literature as a ‘hydrophobic counterion,’ ‘ion pair(ing agent) (IP),’ or ‘salt former.’ Due to their amphiphilic chemical nature, many hydrophobic counterions used are surfactants, so the term ‘surfactant’ may be used as well. The act of forming an ionic association between the two species is termed either ‘hydrophobic ion pairing’ or ‘ionic complexation,’ and the resulting paired species is a ‘hydrophobic complex’ or ‘HIP complex.’ We will discuss later why we do not use the term ‘salt.’

Another important piece of terminology is the stoichiometry between the two species. In the HIP literature, there is no standard convention for reporting the ratio of hydrophilic therapeutic to counterion. Molar ratio (reported either as a ratio of x:y or as a fraction), mass ratio, charge ratio, and N/P ratio – i.e. ratio of positive to negative charges, usually reported as a fraction, from the lipoplex literature – have all been used. Consider a 1300 Da peptide with five cationic groups that is paired with five molecules of a monovalent counterion of molecular weight 280 Da (Fig. 2A). Reporting ratios as drug:counterion, this complex has a molar ratio of 1[thin space (1/6-em)]:[thin space (1/6-em)]5 or 0.2, a mass ratio of 0.93, a charge ratio of 1[thin space (1/6-em)]:[thin space (1/6-em)]1, and an N/P ratio of 1. Charge and molar ratios are the most intuitive of these, and the x[thin space (1/6-em)]:[thin space (1/6-em)]y ratio nomenclature is more intuitive than fractions.


image file: c9na00308h-f2.tif
Fig. 2 Example schematic of hydrophobic ion pairing between a 1.3 kDa peptide and 280 Da anionic surfactants. When reporting charge ratio, it is helpful to specify if the value given is based on the API's net charge (typical for proteins) or total number of one kind of charge.

We recommend that future researchers in the field use charge ratios and report the ratio as ‘drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion’ rather than as a fraction. Charge ratio is a useful and intuitive parameter in HIP, and should be reported whenever possible. Both molecules' degrees of ionisation may vary with pH; when possible, the charge ratio should be reported at the pH of the complexation.11 When describing the charge ratio of a system where one molecule is zwitterionic, researchers should note whether their reported charge ratio is based on the molecule's net charge or charge of only one type. We recommend the latter, but this is not always possible for large proteins, where only net charge can readily be determined. Consider the example above; if the peptide had one anionic group in addition to five cationic groups, the charge ratio of peptide cations (5) to counterion anions (5) is still 1[thin space (1/6-em)]:[thin space (1/6-em)]1 (Fig. 2B). The peptide[thin space (1/6-em)]:[thin space (1/6-em)]counterion charge ratio calculated from the peptide's net charge of (5−1=)4, though, is 4[thin space (1/6-em)]:[thin space (1/6-em)]5 or 1[thin space (1/6-em)]:[thin space (1/6-em)]1.25, suggesting an excess of counterions when none actually exists. Reporting the molar ratio along with the charge ratio should clarify this point, provided an accurate counting of what charged groups exist on each species is included. In this review, we have converted reported stoichiometries into charge ratios to facilitate comparisons.

2. Hydrophobic ion pairing

Hydrophobic ion pairing is an attractive technique for encapsulating water-soluble therapeutics using formulation strategies optimized for water-insoluble drugs. These strategies are desirable because new strategies to encapsulate hydrophilic molecules in nano-scale delivery vehicles remain challenging.12 Low drug loadings, poor encapsulation efficiencies, and a lack of scalability continue to prevent many liposome and nanoparticle formulations of biologic therapeutics from reaching the market.12 The potential benefits of encapsulation – targeting, protection from enzymatic degradation, improved circulation time, enhanced bioavailability, controlled release, reduced toxicity, and overall improved drug performance – are strong driving motivations to develop scalable, highly-loaded formulations with high encapsulation efficiencies.13,14 This is particularly attractive for biologic (peptide and protein) therapeutics, whose circulation time unprotected in the blood may be as low as minutes.12

Nanoparticle formulation strategies for hydrophobic drugs have been developed to address the growing number of new, strongly hydrophobic therapeutics.15,16 These techniques – oil-in-water emulsions, nanoprecipitation, solid lipid nanoparticles, etc. – are designed to take advantage of a drug's hydrophobicity/lipophilicity. They do not translate easily to the encapsulation of hydrophilic therapeutics.17 HIP solves this problem by temporarily modifying the therapeutics to increase their hydrophobicity and allow encapsulation. When the modification is undone, the original hydrophilic therapeutic is regenerated.1 We will discuss ways of controlling dissociation to tune release elsewhere in the review. In many reported cases, the de-complexed released therapeutic remains fully active; this has been shown even for large proteins with tertiary structure-dependent activity.18

Modifying a drug's solubility profile to make it more hydrophobic for encapsulation is also the goal of some prodrug strategies;19 both techniques temporarily add hydrophobic groups to a hydrophilic molecule.20 Unlike prodrug approaches, HIP does not modify any covalent bonds on the original API. This is important from a regulatory standpoint: prodrugs require full FDA approval but the requirements for hydrophobic ion pairs may not be as stringent, depending on the other changes made to the formulation.21

2.1 Thermodynamics

Mechanisms of solubilisation in aqueous solution. Why are molecules soluble or insoluble in aqueous solutions? Understanding the fundamental mechanisms of solubilization helps understand the principles behind HIP. The solubility or phase behaviour of a species is determined by entropy and enthalpy. Entropy is the state of disorder in a system and is determined by the statistical number of configurations a system can attain. For small molecules, that entropy is determined by the concentration of the solute in the solvent. The entropic contribution to the chemical potential for a dilute solute in an ideal system is μideali = μi0 + kT[thin space (1/6-em)]ln[thin space (1/6-em)]xi, where μi is the chemical potential (μi0 is the chemical potential of the pure species) and xi is the molar fraction of the solute. It can be seen that entropy always favours dissolution, i.e. increasing the degrees of freedom in the system is favoured.

There is some subtlety with water as the aqueous solvent, since the hydrogen bonding interactions between water molecules adds an entropy contribution to the water solvent itself.22 That entropic contribution determines observations such as the Hofmeister series, where the specific salt cations and anions influence solubility.23 For this review, we will ignore this effect, since the concept of counter ion binding and precipitation does not require a detailed understanding of water structure.

Water is a unique solvent and is the strongest of the hydrogen bonding fluids. The polarity of the water molecule gives water a high dielectric constant: ε = 80. This is in contrast to the dielectric constant of a hydrophobic oil phase (e.g. dodecane), which will have ε = 2. The dielectric constant determines the strength of electrostatic interactions between elementary charges. The interaction energy between a positive and negative charge in solution is image file: c9na00308h-t1.tif. As the dielectric constant increases, therefore, the force holding ions together decreases. Hydrophobic ion pairs stay insoluble in part because they usually include large nonpolar groups that exclude water from fully solvating the ionic–ionic interaction sites. The hydrophobic ion paired precipitate or core of a NC has a low dielectric constant, which magnifies the strength or the electrostatic attractions. This same concept arises in the protein literature, where the interactions between anionic and cationic peptides in the hydrophobic core of a globular protein enhance its stability. However, the same residues on the surface of a protein would enhance its water solubility. It often remains unclear if any water remains associated with the pair in a nanoparticle core; the best data addressing this question comes from studies of ionomers.24–27

2.2 Eligibility for hydrophobic ion pairing and commonly-used counterions

Eligibility for hydrophobic ion pairing. For a therapeutic molecule to be eligible for HIP, it must contain at least one charged group. Many antibiotics contain amine groups that are positively charged at physiological pH and can be used for this purpose. Anionic carboxylic acid groups are also commonly used as pairing sites in HIP. Molecules with a strong net charge or only one type of charge are the most straightforward to complex, since a single counterion species can be used. Zwitterionic molecules with both anionic and cationic charges present a more complicated challenge; here, shifting the solution pH to turn off one type of charge can be an effective strategy. This is presented in more detail below. Another consideration for HIP eligibility is the molecule's charge density (charge per molecular weight). Intuitively, adding a single hydrophobic counterion onto a small molecule that has a single charge and molecular weight approximately 300 Da will increase hydrophobicity more than adding the same single counterion to a peptide with one charge and a molecular weight of 3000 Da, i.e. the charge per surface area is lower on the larger molecule. Depending on the desired hydrophobicity of the final complex, a given charged molecule may have too low of a charge density, such that adding a hydrophobic counterion will not sufficiently increase hydrophobicity to affect precipitation.

We typically do not use or recommend using the term ‘salt’ to describe the complexes formed by hydrophobic ion pairing, because ‘salts’ are commonly understood to refer to crystalline assemblies of stoichiometric amounts of oppositely-charged ions. HIP complexes may be less crystalline than the original drug used,28–30 and non-stoichiometric charge ratios are common.

We pause here to briefly address the field of nucleic acid encapsulation and delivery. Nucleic acids – plasmid DNA, linear DNA, siRNA, mRNA, etc. – have been packaged into solid lipid nanoparticles (SLNs) or lipoplexes through ionic complexation between cationic lipids and the nucleic acid's anionic phosphate backbone. This strategy shares a number of similarities with hydrophobic ion pairing, with a few notable exceptions. The most significant is that the regular charge along the phosphate backbone gives nucleic acids a strong, uniform charge density along the molecule. This is different from the small molecule, peptide and protein therapeutics discussed here, which often have less ordered regions of hydrophobicity and hydrophilicity/charge. For the reader familiar with HIP but not SLNs/lipoplexes, we recommend a number of reviews.31–37

Common counterions. Because the counterions used for hydrophobic ion pairing should contain at least one charged group and at least one hydrophobic domain, ionic surfactants are common. These may be either anionic or cationic and typically contain either one or two charged groups. Fatty acids or other carboxylic acid-containing surfactants such as oleic acid, stearic acid, or deoxycholic acid, or their sodium salts, have been extensively used. Pamoic acid, which has two carboxylic acid groups, has been effective in cases where fatty acids were not.38 Sulfates are also popular, most frequently sodium dodecyl sulfate and sodium docusate. Two-tailed phospholipids such as dimyristoyl phosphatidyl glycerol have been used as well. Anionic polymers such as dextran sulfate have also been investigated, most frequently for complexation with multivalent peptide or protein therapeutics. Though HIP language has been used to describe this kind of polyelectrolyte complexation, the mechanisms differ in important ways. That distinction is the subject of Section 5 of this review (Table 1).
Table 1 Example anionic counterions used in hydrophobic ion pairing
Name Structure MW, Da pKa log[thin space (1/6-em)]P Used to pair with
1-Hydroxy-2-naphthoic acid (xinafoic acid) image file: c9na00308h-u1.tif 188.2 3.02 2.6 AZD2811 (ref. 38 and 89)
2-Naphthalene sulfonic acid (NSA) image file: c9na00308h-u2.tif 208.2 −1.8 2.14 Atazanavir28
Brilliant blue FCF image file: c9na00308h-u3.tif 792.8 5.83 and 6.58 −1.45 Atenolol155
Carboxy methyl polyethylene glycol (CM-PEG) image file: c9na00308h-u4.tif PEG length not given     Bovine serum albumin56
Lysozyme56
r-met-HuGdNF56
Cholesteryl hemisuccinate image file: c9na00308h-u5.tif 486.7 5.8 8.5 Colistin156
Doxorubicin112
Cholic acid (sodium cholate) image file: c9na00308h-u6.tif 408.6 4.98 2.02 AZD2811 (ref. 38 and 89)
Bovine serum albumin56
Lysozyme56
r-met-HuGdNF56
Insulin157
Decanoic acid (sodium decanoate/sodium caprate) image file: c9na00308h-u7.tif 194.3 4.9 4.09 Octreotide9,96
Dimyristoyl phosphatidyl glycerol (DMPG) image file: c9na00308h-u8.tif 666.9 1.89 9.2 Insulin42
Salmon calcitonin85
Dioleoyl phosphatidic acid (DOPA) image file: c9na00308h-u9.tif 701 1.3 13.2 Doxorubicin71
Gefitinib30
Docosahexaenoic acid image file: c9na00308h-u10.tif 328.5 4.89 6.75 Doxorubicin70
Hexadecylphosphate image file: c9na00308h-u11.tif 320.4   6.38 Doxorubicin158
Thymopentin159
Tobramycin160
Linoleic acid image file: c9na00308h-u12.tif 280.5 4.77 6.8 Vancomycin64
N,N-Dipalmitoyl-L-lysine image file: c9na00308h-u13.tif       Colistin156
Oleic acid (sodium oleate also used) image file: c9na00308h-u14.tif 282.5 5 6.78 AZD2811 (ref. 38 and 89)
Berberine161
Desmopressin77,86
Dorzolamide81
Doxorubicin106,121
Insulin86,102,162
Leuprolide86,94,101
Lumefantrine48
Lycobetaine163
Lysozyme57,58
Octreotide96
OZ439 (ref. 43 and 154)
Polymyxin B78
Salmon calcitonin85
Vincristine164
Pamoic acid (disodium pamoate also used) image file: c9na00308h-u15.tif 388.4 2.68 6.17 AZD2811 (ref. 38)
Bovine serum albumin165
Cinnarizine47
Clozapine47
Donepezil166
Insulin165
Leuprolide165
Polymyxin B78
Sodium acetate image file: c9na00308h-u16.tif 82 4.7 −0.2 Doxorubicin61
Propanolol61
Quinidine sulfate61
Verapamil61
Sodium cholesteryl sulfate image file: c9na00308h-u17.tif 466.3 3.13 4.2 Colistin156
Sodium decanesulfonate (SDES) image file: c9na00308h-u18.tif 244.3   3.75 Doxorubicin116
Sodium deoxycholate image file: c9na00308h-u19.tif 392.6 4.65 3.8 AZD2811 (ref. 38)
Bovine serum albumin165
Ciprofloxacin88
Insulin80,93,165
Lanreotide98
Leuprolide165
Mitoxantrone diHCl79
Octreotide9,96
Papain97
Salmon calcitonin85
Sodium docusate (AOT, sodium dioctyl sulfosuccinic acid, sodium bis-2- ethylhexyl-sulfosuccinate) image file: c9na00308h-u20.tif 444.6 −0.75 5.2 α-Chymotrypsin167
Atazanavir28
AZD2811 (ref. 38 and 89)
Bevacizumab168
Bovine serum albumin56,169
Cisplatin83
Concanavalin A167
Desmopressin45,77,86,170
Doxorubicin116
Gentamycin82,117–119,171
Irinotecan29
Lanreotide98
Leuprolide45,84,86,110,172
Lysozyme56
Minocycline173
Mtb8.4 (ref. 174)
Naloxone117
Naltrexone117
Octreotide9
r-met-HuGdNF56
Tobramycin175
Trypsin167
Vancomycin176
Sodium dodecyl benzenesulfonate (SDBS) image file: c9na00308h-u21.tif 348.5 −1.7 3.73 Polymyxin B78
Sodium dodecyl sulfate (sodium lauryl sulfate) image file: c9na00308h-u22.tif 288.4 −1.5 1.6 Bovine serum albumin56
Desmopressin77,86
Dorzolamide81
IGG-Fab fragment90
Insulin49,58,84,86,111,177,178
Irinotecan29
Leuprolide11,84,86
Lysozyme18,56,57
Melittin109
Octreotide92,96
Polymyxin B78
r-met-HuGdNF56
Sodium laurate (sodium dodecanoate) image file: c9na00308h-u23.tif 222.3 4.95 5.3 Bovine serum albumin165
Insulin165
Leuprolide165
Sodium n-octadecyl sulfate (sodium stearyl sulfate) image file: c9na00308h-u24.tif 372.5   6.8 Desmopressin77
Lanreotide98
Sodium stearate (stearic acid also used) image file: c9na00308h-u25.tif 306.5 4.7 8.23 Desmopressin77
Doxorubicin61
Propanolol61
Quinidine sulfate61
Verapamil61
Sodium stearoyl glutamate (SSG) image file: c9na00308h-u26.tif 435.6   6.3 Bovine serum albumin165
Insulin165
Leuprolide165
Sodium taurodeoxycholate (STDC) image file: c9na00308h-u27.tif 499.7 −0.94 4.5 Doxorubicin72,95,116
Idarubicin95
Sodium tetradecyl sulfate image file: c9na00308h-u28.tif 316.4 −1.1 5.04 Doxorubicin95
Idarubicin95
Sodium tripolyphosphate image file: c9na00308h-u29.tif 367.9 0.89 −1.9 Irinotecan29
Taurocholic acid (sodium taurocholate also used) image file: c9na00308h-u30.tif 515.7 1.4 0.79 Bovine serum albumin56
Lanreotide98
Lysozyme56
r-met-HuGdNF56
IGG-Fab fragment90
Vitamin E (α-tocopherol) succinate image file: c9na00308h-u31.tif 530.8 4 10.2 Doxorubicin105


The most common cations in the HIP literature are quaternary amines and alkylamines (see Table 2). Quaternary amines are permanently charged, so complexation is possible over a wider range of pH values than primary, secondary, or tertiary amines. The permanent charge is usually cytotoxic, and using quatamines adds toxicity to otherwise nontoxic formulations.39 A wide variety of quaternary amines is commercially available, with varying lengths and numbers of alkyl tails that lead to an easily tuneable range of hydrophobicities.40 Researchers have recently reported efforts to synthesize arginine-based cationic surfactants for HIP, which should be both biodegradable and non-cytotoxic.41

Table 2 Example cationic counterions used in hydrophobic ion pairing
Name Structure Mol. wt. pKa log[thin space (1/6-em)]P Paired with
Arginine-hexadecanoyl ester (AHE) image file: c9na00308h-u32.tif 398.6   0.19 Daptomycin41
Heparin41
Arginine-nonyl ester (ANE) image file: c9na00308h-u33.tif 300.5   −0.06 Daptomycin41
Heparin41
Benethamine(N-benzyl-2-phenylethanamine) image file: c9na00308h-u34.tif 211.3   3.6 Retinoic acid65,108,115
Chitosan image file: c9na00308h-u35.tif Varies     Insulin53
Dodecylamine (laurylamine) image file: c9na00308h-u36.tif 185.3 10.6 5.2 Retinoic acid46,107,114
Hexadecyl trimethylammonium(cetrimonium) bromide (CTAB) image file: c9na00308h-u37.tif 364.5 2.69 Ovalbumin39
Pemetrexed103
Poly(I:C)39
Maprotiline image file: c9na00308h-u38.tif 277.4 10.5 5.1 Retinoic acid115
Nα-Deoxycholyl-L-lysyl-methylester image file: c9na00308h-u39.tif 534.8   3.8 Pemetrexed4
N,N′-Dibenzyl ethylenediamine(benzathine) image file: c9na00308h-u40.tif 240.3   2.86 α-Lipoic acid47
N,N-Dimethyl dodecylamine (DDA) image file: c9na00308h-u41.tif 213.4 9.97 5.91 Am80 (ref. 40)
N,N-Dimethyl hexylamine image file: c9na00308h-u42.tif 129.2 10.4 2.72 Am80 (ref. 40)
N,N-Dimethyl octadecylamine(dimethyl stearamine) image file: c9na00308h-u43.tif 297.6   8.8 Am80 (ref. 40)
Stearylamine(octadecylamine) image file: c9na00308h-u44.tif 269.5 10.7 7.7 Retinoic acid46,65,107,114
Tetrabutyl ammonium bromide (TBAB) image file: c9na00308h-u45.tif 322.4 2.1 Bromothymol blue66
Rose bengal66
Tetraheptyl ammonium bromide (THA) image file: c9na00308h-u46.tif 490.7 8.16 Isoniazid methanesulfonate179
Tetrahexyl ammonium bromide image file: c9na00308h-u47.tif 434.6 6.16 Bromothymol blue66
Rose bengal66
Tetraoctyl ammonium bromide (TOAB) image file: c9na00308h-u48.tif 546.7 9.16 Bromothymol blue66
Rose bengal66
Tetrapentyl ammonium bromide (TPA) image file: c9na00308h-u49.tif 378.5 4.14 Isoniazid methanesulfonate179
Triethylamine (TEA) image file: c9na00308h-u50.tif 101.2 10.8 1.65 Retinoic acid46,65,107,114


Specific considerations by drug molecule class.
Small molecules. Many small molecule drugs have only one ionic group. Depending on the pKa of the ionic group and the drug's solubility, HIP is relatively straightforward and can be carried out in water. In a typical ‘pre-forming’ scenario for hydrophilic small molecules, the drug and counterion are each dissolved in water and mixed to form a precipitate.11,42 It is worth noting that small molecules with ionizable groups may be manufactured either as a salt or in the free acid/base form. The free acid/base is usually less soluble in water than the salt, but might not be hydrophobic enough for a desired encapsulation strategy.43 Since species must be charged in order to ion pair, salt forms of the drug and hydrophobic counterion may be preferred. When the drug is manufactured in the free acid/base form, conversion to a readily-dissociating salt form (e.g. mesylate, ammonium, or sodium) before HIP may assist complexation. A drawback of this approach is that it increases the solution's overall ionic strength, which can drive decomplexation and drug release from a delivery vehicle by ion exchange.38,44,45 Researchers should examine the effect of ionic strength on their specific systems to determine if one charge equivalent of soluble counterions such as sodium or ammonium will noticeably affect release.

Some ionic small molecule drugs such as lumefantrine (for structure, see Table 3) are already hydrophobic, so it is not possible to form an aqueous solution as the starting point for HIP. Hydrophobic ion pairing an already-hydrophobic drug can be useful – for example, to decrease drug crystallinity30,46,47 – but the complex formation is more challenging. Lumefantrine's tertiary amine has a pKa of 8.7, but the drug's log[thin space (1/6-em)]P of 9.2 severely limits its ability to dissolve, and the amine to become charged, in water.48 Dissolving lumefantrine free base in a nonpolar solvent such as tetrahydrofuran guarantees dissolution, but the extent of the amine's charge is more difficult to control and measure in a non-aqueous environment. As mentioned above, conversion to a salt form before complexation may be useful (Table 4).

Table 3 Examples of hydrophobic ion pairing, sorted by therapeutic
Name Structure/etc. Paired with Formulation technique
α-Chymotrypsin 25 kDa protein, 241 residues, pI: 8.75 Sodium docusate167 Solvent evaporation with polymethyl methacrylate, polystyrene, or poly(vinyl acetate)167
α-Lipoic acid image file: c9na00308h-u51.tif N,N′-Dibenzylethylene diamine (DBDA),47 note: included pamoic acid to frustrate αLA[thin space (1/6-em)]:[thin space (1/6-em)]DBDA recrystallization and improve encapsulation PLA-b-PEG NPs by Flash NanoPrecipitation, in situ HIP47
Am80 image file: c9na00308h-u52.tif N,N-Dimethyldodecyl amine (DDA)40 Block copolymer micelles by evaporation-sonication40
N,N-Dimethylhexyl amine40
N,N-Dimethyloctadecyl amine40
Atazanavir image file: c9na00308h-u53.tif 2-Naphthalene sulfonic acid28 SEDDS28
Sodium docusate (AOT)28
Atenolol image file: c9na00308h-u54.tif Brilliant blue FCF155 PLGA NPs by nanoprecipitation155
AZD2811 image file: c9na00308h-u55.tif Oleic acid38,89 Oil in water (o/w) nanoemulsification solvent extraction to form PLA-PEG NPs using in situ HIP38,89
1-Hydroxy-2-naphthoic acid38,89
Cholic acid38,89
Sodium deoxycholate38
Docusate sodium38,89
Pamoic acid38
Berberine image file: c9na00308h-u56.tif Oleic acid161 Liquid crystalline nanoparticulates by a hydrotrope method161
Bevacizumab 149 kDa antibody Docusate sodium168 Lipid coacervation168
Bovine serum albumin (BSA) 66.5 kDa protein, 583 residues, pI: 4.7 Cholic acid56 Double emulsion56
CM-PEG56 Single emulsion56
Sodium dodecyl sulfate56  
Taurocholic acid56  
Sodium docusate56 Double emulsion56
Single emulsion56
SEDDS169
Dextran sulfate91 Solid in oil in water (S/O/W) to form PLGA NPs91
Sodium deoxycholate165 SEDDS165
Sodium laurate165
Sodium stearoyl glutamate165
Pamoic acid disodium165
Bromothymol blue image file: c9na00308h-u57.tif Tetrabutylammonium bromide66 Encapsulated into polystyrene microparticles using compressed carbon dioxide66
Tetrahexylammonium bromide66
Tetraoctylammonium bromide66
Chlorhexidine image file: c9na00308h-u58.tif Losartan152 Nanoprecipitation152
Cinnarizine image file: c9na00308h-u59.tif Pamoic acid,47 note: Also unsuccessfully tried camphor-10 sulfonic acid (micellized), cinnamic acid, palmitic acid, and oleic acid PLA-b-PEG NPs by Flash NanoPrecipitation, in situ HIP47
Ciprofloxacin image file: c9na00308h-u60.tif Sodium deoxycholate88 Oil-in-water (o/w) submicron emulsion88
Cisplatin image file: c9na00308h-u61.tif Sodium docusate83 Stearic acid coacervation83
Clozapine image file: c9na00308h-u62.tif Pamoic acid47 PLA-b-PEG NPs by Flash NanoPrecipitation, in situ HIP47
Colistin image file: c9na00308h-u63.tif Cholesteryl hemisuccinate156 PLA NPs by emulsion evaporation156
N,N-Dipalmitoyl-L-lysine156
Sodium cholesteryl sulfate156
Concanavalin A 104–112 kDa protein (tetramer), pI: 4.5–5.5 Sodium docusate167 Solvent evaporation with polymethyl methacrylate, polystyrene, or poly(vinyl acetate)167
Dalargin image file: c9na00308h-u64.tif Dextran sulfate104 PLGA-PEG NPs by S/O/W emulsion104
Daptomycin image file: c9na00308h-u65.tif Arginine-hexadecanoyl ester41 N/A; proof-of-concept HIP using novel cationic surfactants demonstrates precipitation and increased log[thin space (1/6-em)]P41
Arginine-nonyl ester41
Desmopressin image file: c9na00308h-u66.tif Oleic acid77 SEDDS45,77,86,170
Sodium docusate45,77,86,170
Sodium dodecyl sulfate77,86
Sodium stearate77 (note: less effective than SDS, AOT, and oleate)
Sodium stearyl sulfate77 (note: less effective than SDS, AOT, and oleate)
Dexamethasone valine valine prodrug image file: c9na00308h-u67.tif Dextran sulfate120 PLGA NPs by S/O/W emulsion120
Donepezil image file: c9na00308h-u68.tif Pamoic acid166 High pressure homogenization with D-α-tocopherol polyethylene glycol 1000 succinate166
Dorzolamide image file: c9na00308h-u69.tif Oleic acid81 PLGA NPs or PEG3-PSA microparticles by S/O/W emulsion81
Sodium dodecyl sulfate81
Doxorubicin image file: c9na00308h-u70.tif Alginic acid61 Microemulsion by stearic acid coacervation61
Cholesteryl hemisuccinate112 Thin film dispersion112
Dextran sulfate61,95 Microemulsion by stearic acid coacervation61
Warm wax microemulsion solvent evaporation95
Dioleoyl phosphatidic acid (DOPA)71 PLA-b-PEG NPs by nanoprecipitation71
Docosahexaenoic acid70 SLNs by hot melt ultrasound emulsification70
Hexadecylphosphate158 SLNs by warm oil-in-water microemulsion with stearic acid and taurocholate sodium158
Hyaluronic acid153 Thin film dispersion by lipid film hydration with suspended HIP complex and homogenization153
Oleic acid106,121 70 °C high-pressure homogenization121
High-pressure film homogenization106
Sodium acetate61 Microemulsion by stearic acid coacervation61
Sodium alginate61 Microemulsion by stearic acid coacervation61
Sodium decanesulfonate116 Microemulsion by stearic acid coacervation116
Sodium docusate116 Microemulsion by stearic acid coacervation116
Sodium stearate61 Microemulsion by stearic acid coacervation61
Sodium taurodeoxycholate72,95,116 Warm wax microemulsion solvent evaporation95
Microemulsion by stearic acid coacervation116
Microemulsion by shear and ultrasonic homogenization after drying from molten stearyl alcohol72
Sodium tetradecyl sulfate95 Warm wax microemulsion solvent evaporation95
Vitamin E succinate105 SLNs by hot melt ultrasound emulsification105
Gefitinib image file: c9na00308h-u71.tif Dioleoyl phosphatidic acid (DOPA)30 Nanoprecipitation with doxorubicin-conjugated PLA-b-PEG NPs30
Gentamicin image file: c9na00308h-u72.tif Sodium docusate82,117–119,171 PLA microparticles by precipitation with compressed antisolvent117,171
Microparticles by PCA using stabilizer poly(methyl vinyl ether-co-maleic anhydride)118
PCA with no stabilizer82,119
PLGA NPs by emulsion solvent evaporation82,119
Heparin image file: c9na00308h-u73.tif Arginine-hexadecanoyl ester41 N/A; proof-of-concept HIP using novel cationic surfactants demonstrates precipitation and increased log[thin space (1/6-em)]P41
Arginine-nonyl ester41
Idarubicin image file: c9na00308h-u74.tif Dextran sulfate95 Warm wax microemulsion solvent evaporation95
Sodium taurodeoxycholate95
Sodium tetradecyl sulfate95
IGG-Fab fragment 48 kDa protein Sodium dodecyl sulfate90 Modified nanoprecipitation90
Taurocholic acid90 S/O/W PLGA NPs90
Dextran sulfate90  
Insulin 5.8 kDa peptide, 51 residues (6 cationic and 6 anionic), pI: 5.3 Cholic acid157 Reverse micelle-double emulsion using palmitic and stearic acid157
Chitosan53 Homogenization and stabilization with SDS53
Dimyristoyl phosphatidyl glycerol42 SNEDDS42
Oleic acid58,102,162 S/O/W emulsion58
PLGA NPs by emulsion solvent diffusion102,162
Pamoic acid disodium165 SEDDS165
Sodium laurate165
Sodium stearoyl glutamate165
Sodium deoxycholate80,93,165 PLGA NPs by emulsion solvent diffusion93
S/O/W emulsion80
SEDDS165
Sodium docusate84,86 SEDDS86
Stearic acid coacervation84
Sodium dodecyl sulfate49,84,111,177,178 Stearic acid coacervation84
PLGA NPs by emulsion solvent diffusion111,177,178
Electrospray with stearic or pamoic acid49
Irinotecan image file: c9na00308h-u75.tif Sodium docusate29 PEG-b-PLGA NPs via water/oil/water double emulsion; in situ HIP29
Sodium dodecyl sulfate29
Sodium tripolyphosphate29
Isoniazid methanesulfonate image file: c9na00308h-u76.tif Tetraheptylammonium bromide179 Precipitation with compressed antisolvent (PCA)179
Tetrapentylammonium bromide179
Lanreotide image file: c9na00308h-u77.tif Sodium deoxycholate98 SNEDS98
Sodium docusate98
Sodium stearyl sulfate98
Taurocholic acid98
Leuprolide image file: c9na00308h-u78.tif Oleic acid94,101 PLGA microspheres by O/W emulsion101
SMEDDS94
Sodium deoxycholate165 SEDDS165
Sodium laurate165
Sodium stearoyl glutamate165
Pamoic acid disodium165
Sodium docusate45,84,86,172 SEDDS45,86
Stearic acid coacervation84
Oligosaccharide ester microparticles by spray drying172
Solid lipid nanoparticles and nanostructured lipid carriers by high pressure homogenization110
Sodium dodecyl sulfate11,84 Stearic acid coacervation84
Hydrogen bonding complexation between polyacrylic acid and Pluronic F68 (ref. 11)
Sodium stearate87 Solid lipid NPs by: solvent diffusion87
Oil-in-oil (O/O) emulsion-evaporation87
Loperamide image file: c9na00308h-u79.tif Dextran sulfate104 PLGA-PEG NPs by S/O/W emulsion104
Losartan image file: c9na00308h-u80.tif Chlorhexidine152 Nanoprecipitation152
Lumefantrine image file: c9na00308h-u81.tif Oleic acid48 SEDDS48
Lycobetaine image file: c9na00308h-u82.tif Oleic acid163 Emulsion by lipid film hydration high-pressure homogenization163
Lysozyme 14.4 kDa protein, 129 residues, pI: 11.35 Cholic acid56 Double emulsion56
Single emulsion56
CM-PEG56 Double emulsion56
Single emulsion56
Dextran sulfate59 Emulsion solvent diffusion59
Oleic acid57,58 PLGA NPs by emulsion diffusion57
S/O/W emulsion58
Sodium docusate56 Double emulsion56
Single emulsion56
Sodium dodecyl sulfate18,57 PLGA NPs by emulsion diffusion57
S/O/W emulsion: Polymer/lipid NPs18
Taurocholic acid56 Double emulsion56
Single emulsion56
Melittin 2.8 kDa peptide, 26 residues, pI: 12.01 Sodium dodecyl sulfate109 PLGA nanoparticles by emulsion solvent diffusion109
Minocycline image file: c9na00308h-u83.tif Sodium docusate173 PLGA NPs by emulsion-solvent-diffusion173
Mitoxantrone dihydrochloride image file: c9na00308h-u84.tif Sodium deoxycholate79 Nanoprecipitation79
Mtb8.4 Protein, TB antigen, pI: 6.3 Sodium docusate174 PLG microspheres by emulsification174
Naloxone image file: c9na00308h-u85.tif Sodium docusate117 PLA microparticles by precipitation with compressed antisolvent117
Naltrexone image file: c9na00308h-u86.tif Sodium docusate117 PLA microparticles by precipitation with compressed antisolvent117
Octreotide image file: c9na00308h-u87.tif Dextran sulfate92 S/O/W emulsion92
Oleic acid96 SNEDDS96
Sodium decanoate9,96 SNEDDS96
SEDDS9
Sodium deoxycholate9,96 SNEDDS96
SEDDS9
Sodium docusate9 SEDDS9
Sodium dodecyl sulfate92,96 S/O/W emulsion92
SNEDDS96
Ovalbumin (OVA) 43 kDa protein, 385 residues, pI: 5.19 Cetrimonium bromide (CTAB)39 pH-sensitive polyketal microparticles by single emulsion39
OZ439 mesylate (artefenomel) image file: c9na00308h-u88.tif Sodium oleate43,154 HPMCAS NPs by Flash NanoPrecipitation; in situ HIP43,154
Papain 23.4 kDa protein, 212 residues, pI: 8.8–9.6 Sodium deoxycholate97 SEDDS97
Pemetrexed image file: c9na00308h-u89.tif Cetrimonium bromide (CTAB)103 Lyotropic liquid crystalline nanoparticles by homogenization (in situ HIP)103
Nα-Deoxycholyl-L-lysyl-methylester4 W/O/W emulsion4
Polymyxin B image file: c9na00308h-u90.tif Oleic acid sodium salt78 PCL-b-PEG NPs by Flash NanoPrecipitation (FNP), in situ HIP,78 note: sodium decanoate, myristate, deoxycholate, 2-naphthalenesulfonate, 1-heptanesulfonate, 1-octane-sulfonate, and 1-decanesulfonate formed a precipitate when mixed with polymyxin B at 1[thin space (1/6-em)]:[thin space (1/6-em)]1 charge ratio but did not form NPs by FNP. Sodium hexanoate, benzenesulfonic acid, camphorsulfonic acid, and 1,2-ethanesulfonate did not form a precipitate when mixed with polymyxin B at 1[thin space (1/6-em)]:[thin space (1/6-em)]1 charge ratio.
Pamoic acid sodium salt78
Sodium dodecyl sulfate78
Sodium dodecyl benzenesulfonate78
Poly(inosinic acid)-poly (cytidylic acid) (poly(I[thin space (1/6-em)]:[thin space (1/6-em)]C)) Double-stranded RNA analog, TLR3 agonist Cetrimonium bromide (CTAB)39 pH-sensitive polyketal microparticles by single emulsion39
Propranolol image file: c9na00308h-u91.tif Alginic acid61 Microemulsion by stearic acid coacervation61
Dextran sulfate61
Sodium acetate61
Sodium stearate61
Quinidine sulfate image file: c9na00308h-u92.tif Alginic acid61 Microemulsion by stearic acid coacervation61
Dextran sulfate61
Sodium acetate61
Sodium stearate61
r-met-HuGdNF Recombinant methionyl human Glial-cell line derived neurotrophic factor Cholic acid56 Double emulsion56, single emulsion56
CM-PEG56
Sodium docusate56
Sodium dodecyl sulfate56
Taurocholic acid56
Retinoic acid image file: c9na00308h-u93.tif Benethamine65,108,115 Hot melt homogenization using ultrasound emulsification41–43,65,108,115
Laurylamine46,107,114
Maprotiline (both HCl and free base)115
Stearylamine46,65,107,114
Triethylamine46,65,107,114
Rose bengal image file: c9na00308h-u94.tif Tetrabutylammonium bromide66 Encapsulated into polystyrene microparticles using compressed carbon dioxide to plasticize polystyrene MPs and allow diffusion in66
Tetrahexylammonium bromide66
Tetraoctylammonium bromide66
Salmon calcitonin 3.4 kDa peptide, 32 residues, pI: 8.86 Dimyristoyl phosphatidyl glycerol (DMPG)85 PLGA NPs by solvent diffusion85
Oleic acid85
Sodium deoxycholate85
Thymopentin image file: c9na00308h-u95.tif Hexadecylphosphate159 Warm oil in water microemulsion159
Tobramycin image file: c9na00308h-u96.tif Hexadecylphosphate160 Warm oil in water microemulsion160
Sodium docusate175 PLGA NPs by O/W emulsion175
Trypsin 23 kDa protein, 220 residues, pI: 10.1–10.5 Sodium docusate167 Solvent evaporation with polymethyl methacrylate, polystyrene, or poly(vinyl acetate)167
Vancomycin image file: c9na00308h-u97.tif Linoleic acid64 Hot homogenization and ultrasonication64
Sodium docusate176 SEDDS176
Verapamil image file: c9na00308h-u98.tif Alginic acid61 Microemulsion by stearic acid coacervation61
Dextran sulfate61
Sodium acetate61
Sodium stearate61
Vincristine image file: c9na00308h-u99.tif Oleic acid164 High pressure homogenization164


Table 4 Examples of some polyvalent counterions used to encapsulate charged APIs. For a more complete survey of polyelectrolyte coacervation, see ref. 124–141
Name Structure MW, Da pKa log[thin space (1/6-em)]P Used to pair with:
Anions
Alginic acid (sodium alginate also used) image file: c9na00308h-u100.tif Varies 1.5–3.5 −1.5 Doxorubicin61
Propanolol61
Quinidine sulfate61
Verapamil61
Dextran sulfate image file: c9na00308h-u101.tif Varies <2   Bovine serum albumin91
Dalargin104
Dexamethasone valine valine prodrug120
Doxorubicin61,95
Idarubicin95
IGG-Fab fragment90
Loperamide104
Lysozyme59
Octreotide92
Propanolol61
Quinidine sulfate61
Verapamil61
Hyaluronic acid image file: c9na00308h-u102.tif Varies 2.9 −8.2 Doxorubicin153
[thin space (1/6-em)]
Cations
Chitosan image file: c9na00308h-u103.tif Varies     Insulin53



Peptides. Many antibiotic peptides such as nisin and colistin (for structure, see Table 3) are cationic and strongly water soluble, with log[thin space (1/6-em)]P values less than 0. Basic amino acid residues in the peptide (lysine, histidine, arginine) are positively charged at physiological or acidic pH and are sites for ion pairing. Some cationic peptide drugs are manufactured as sulfate salts that dissociate readily in water and do not have the same solubility and ionization challenges as hydrophobic small molecules. For peptides with only cationic charges such as polymyxin B, aqueous complexation with anionic surfactants is straightforward. Zwitterionic peptides are more challenging, however. If a peptide contains both cationic and anionic groups, it is possible that complexing only the cationic sites and leaving anionic sites charged and exposed (or vice versa) will impart sufficient hydrophobicity for the desired application. This is especially true when one kind of charged site significantly outnumbers the other, as in the case of a COOH-terminated peptide with five cationic sites. Complexing five out of the six charged sites with hydrophobic counterions may reduce water solubility enough to enable encapsulation.

When there are approximately the same number of cationic and anionic sites on a zwitterionic peptide, though, complexing only one charge may not be sufficient. It is preferable to use only one counterion species to complex a molecule, rather than adding both anionic and cationic hydrophobic counterions (which will invariably pair with each other and precipitate, complicating stoichiometry and adding difficult-to-separate insoluble salts to the system) in an attempt to complex every charged site. In this case, shifting the pH to turn off one type of charge is a valid approach. Consider insulin, a 5.8 kDa peptide with 51 residues, 6 of which are cationic and 6 anionic. Insulin has no net charge at its isoelectric point at pH 5.3. Researchers have reported shifting the solution pH either up or down from 5.3 to deprotonate insulin's basic residues or protonate its acidic residues, respectively.42,49–53 With only one type of charge, the peptide can then be hydrophobically ion paired (Fig. 3).


image file: c9na00308h-f3.tif
Fig. 3 Schematic illustrating the pH-shifting strategy using glycine as a model API. At low pH, carboxylic acid groups are protonated and uncharged. At high pH, animes are deprotonated and uncharged. For some zwitterionic APIs, researchers have reported shifting pH to one extreme to turn off one type of charge prior to ion pairing.

Researchers should consider several factors when using a pH shifting strategy. First, peptides are subject to degradation under basic conditions, so shifting the pH to strongly acidic is likely preferable.54 Second, the complexing counterions are subject to protonation or deprotonation under extreme pH conditions as well. Insulin has only cationic charges at pH 1.5, but an anionic fatty acid counterion such as oleic acid (pKa ∼ 5) will be protonated under those conditions too. A much more acidic counterion such as sodium dodecyl sulfate (pKa −1.5) or sodium docusate (pKa −0.75) must be used. These sulfate surfactants are less biocompatible than fatty acids, in part because of this difference in pKa. The same considerations apply when shifting the pH to basic. Quaternary amines may be the only groups to reliably retain their cationic charge at a high pH, but using these cytotoxic surfactants to complex an anionic peptide presents its own challenges.


Proteins. Protein therapeutics are commonly zwitterionic, and all the considerations of net charge, ratio of basic to acidic residues, pI, and pH shifting that apply to zwitterionic peptides also apply to proteins. An additional complication when complexing proteins is their sensitivity to denaturation. Some surfactants such as sodium dodecyl sulfate disrupt tertiary structure and cause proteins to denature.55 Using ‘gentler’ surfactants such as fatty acids may cause less degradation, but might also prevent the pH shifting approaches discussed above.

A popular model protein for hydrophobic ion pairing and encapsulation is lysozyme, which is cationic at physiological pH.18,56–59 Lysozyme's enzymatic activity can be easily measured via a cell lysis assay; therefore, testing whether or not the protein was denatured during complexation, encapsulation, and release is straightforward. Devrim et al. found that even when using sodium dodecyl sulfate as an ion pairing agent, released lysozyme retained over 80% of its enzymatic activity.18 Yoo et al. reported that the enzyme was more stable in DMSO when ion paired using SDS or oleate, and postulated that HIP complexation could help stabilize a protein's tertiary structure.57 Notably, lysozyme tends to refold into its native active form, so not all techniques that claim to ‘retain’ the protein's activity will do so for all enzymes.

2.3 Key parameters for hydrophobic ion pairing

The following section is intended to guide the reader in choosing an effective hydrophobic counterion for a given encapsulation and/or delivery system. It is important to note that the goals for a given delivery system – e.g. drug chemistry, drug loading, encapsulation technique, biological target, release profile, etc. – are the most important factors when choosing a suitable counterion. This section will overview how parameters such as drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion charge ratio and counterion chemistry affect those goals.
Counterion chemistry: hydrophobicity. The log[thin space (1/6-em)]P, the logarithm of the octanol–water partition coefficient, is a typical measure of hydrophobicity that is convenient for HIP. For a given charged head group, the longer or more saturated an alkyl tail, or the more alkyl tails, the higher the log[thin space (1/6-em)]P. Stearic acid (lipid number 18[thin space (1/6-em)]:[thin space (1/6-em)]0), for example, has a higher log[thin space (1/6-em)]P than both capric acid (lipid number 10[thin space (1/6-em)]:[thin space (1/6-em)]0) and oleic acid (lipid number 18[thin space (1/6-em)]:[thin space (1/6-em)]1). Quaternary amines also follow this trend, though their alkyl tails are fully saturated. Dimethyl dihexadecyl ammonium bromide (two methyl tails and two C16 tails) is more hydrophobic than CTAB (three methyl tails and one C16 tail), and tetraheptyl ammonium bromide (four C7 tails) is more hydrophobic than tetrabutyl ammonium bromide (four C4 tails). Note that log[thin space (1/6-em)]P values for a free acid/base or an ionized surfactant may be different when reported from measurements or calculations. In general, the higher the log[thin space (1/6-em)]P of the counterion used, the higher the log[thin space (1/6-em)]P of the resulting complex.40,60

The most hydrophobic counterion is not always the best to use. Increasing alkyl tail length or number of tails increases molecular weight, meaning the final complex will have a lower mass fraction of drug. This drives down drug loading in a delivery vehicle, all else (charge ratio, encapsulation efficiency, etc.) being equal. Availability and cost are another factor, since not all fatty acids or quaternary amines are commercially available at high purity and low cost. Solubility limitations are discussed in the following paragraph. Finally, comparing log[thin space (1/6-em)]P values among fatty acids is straightforward, but it is difficult a priori to compare the effect of a fatty acid vs. a bile acid or other carboxylic acid surfactant (e.g. oleic acid vs. pamoic acid, which is divalent) on complexation.

Extremely hydrophobic counterions, particularly those with protonated (free acid) carboxylic head groups, are difficult to dissolve in water for ion pairing. For the pairing to be effective, care should be taken to ensure that both species are dissolved and ionized prior to complexation. We recommend using a counterion's most water-soluble salt form, usually a sodium salt for anions and a bromide salt for cations.61 For example, oleic acid is sparingly soluble in water, but sodium oleate is water-soluble up to 10 wt%.62,63

When choosing among different counterions with various log[thin space (1/6-em)]P values, it is important to keep in mind why HIP is needed. This will vary by the encapsulation technique used. For example, when using nanoprecipitation, the primary goal of complexation is to decrease water solubility. When using an emulsion or SLN approach, however, the main goal is to increase lipophilicity. These distinctions will be discussed in further detail in Section 3, which focuses on encapsulation strategies, but we will give a brief example here. Consider vancomycin, a 1450 Da peptide with a single ionisable primary amine. We have found that vancomycin cannot be made to precipitate in Flash NanoPrecipitation, even using HIP, due to its low charge density. Kalhapure et al., however, improved vancomycin encapsulation efficiency from 16.8% to and 70.7% by preforming a vancomycin[thin space (1/6-em)]:[thin space (1/6-em)]linoleic acid complex prior to formulation by hot homogenization and ultrasonication using the solid lipid Compritol 888 ATO and additional surfactants.64 It is likely that vancomycin's increased lipophilicity, rather than improved hydrophobicity, led to this result. Adding oleate's 18-carbon tail to vancomycin likely improved the API's ability to interact with and remain associated with Compritol 888's alkyl tail.

A counterion's log[thin space (1/6-em)]P value is therefore not the only factor to consider when considering hydrophobicity.56 It is important to remember that in addition to excluding water, hydrophobic domains on a counterion can interact hydrophobically and sterically with (1) one another, (2) hydrophobic domains on the complexed drug, and (3) the delivery vehicle's polymers, lipids, or surfactants.65,66 Hydrophobic interactions may make a counterion with aromatic groups more suitable for use than one with an aliphatic tail, for example, or give rise to favourable cooperativity between a drug and counterion with an unsaturated aliphatic tail, even though one with a saturated tail may have a higher log[thin space (1/6-em)]P. These interactions remain an active area of research.

Counterion chemistry: pKa and pH. Counterions must be charged to ionically complex. Sulfate and sulfonate anions and quaternary amine cations are essentially always charged in aqueous environments, but the degree of ionization for carboxylic acids and primary, secondary, and tertiary amines varies with pH. Therefore pH and pKa (of the drug molecule and the counterion) are both important to consider during HIP. Operating at a pH near one species' pKa value is not advised, because charge ratios are difficult to predict and control when one species is only partially ionized. Fig. 4 illustrates the pH window over which polymyxin B and oleic acid can be paired.
image file: c9na00308h-f4.tif
Fig. 4 An example species diagram showing the percent ionization of polymyxin B and oleic acid as a function of pH. From approximately pH 6.5 to 9, both species are nearly 100% ionized and could be paired with clear expectations about the resulting complex's charge ratio.

For peptide and protein drugs with many ionizable groups, the isoelectric point pI is a straightforward parameter to use, rather than trying to account for the pKa and ionizable state of each charged residue. As in charged polymers, the curve of charge versus pH for proteins is typically broader about the pI than an individual monomer would be. Curves denoting net charge versus pH are available for many proteins in the literature.67–69

When either the drug or counterion used has a carboxylic acid or non-quaternary amine head group, the resulting complex may demonstrate pH-sensitive dissociation, which can be used to tune drug release. pH-dependent release is useful in drug delivery, for example, for targeting to endosomes or tumors. Cationic peptides are popular in the HIP literature; these are positively charged at physiological and acidic pHs, so pH-dependent release could be accomplished by pairing them with fatty acids, rather than sulfates or phosphates. At a pH below the acid's pKa, carboxylic acid become protonated, forming the uncharged free acid and decomplexing from their cationic counterparts. Hydrophobic and steric interactions from the former ion pair remain effective, but faster drug release can be expected.30,70–72 This will be discussed in more detail in the section on drug release.

Pinkerton et al. note that the pKa values of the two charged species should be different by at least two pH units for an ion pair to reliably form. Importantly, the authors pointed out that solvent quality affects pKa values. Therefore, when complexing in a mixed solvent of water and organics increasing the volume fraction of water may be useful to ensure complexation between an anion and cation with pKa values close to neutral.47,73,74 Other researchers have noted that physical confinement, e.g. in a delivery vehicle, may affect pKa values as well; this phenomenon has the potential to affect HIP, and further study is needed75,76.

An interesting study that to our knowledge has not been carried out in the literature would examine pH-sensitive ion paired drug release behavior as a function of counterion head group. For example, Zupancic et al. paired cationic desmopressin with both sodium n-octadecyl sulfate and sodium stearate.77 The two have aliphatic tails of similar lengths, but the former has a sulfate head group and the latter has a carboxylic acid. If paired with a cationic API and encapsulated (ceteris paribus, and in a system with no other ionic or pH-sensitive components), we would expect the n-octadecyl sulfate system's release profile not to vary between pH values of e.g. 6.5, 4.5, and 2.5. The system containing stearate should release differently at the three pH values, since stearate's pKa is 4.7. Zupancic et al. found that sodium docusate and sodium oleate complexed with and precipitated desmopressin more effectively than either stearate or n-octadecyl sulfate, so the latter two counterions were not examined further. Both counterions must effectively complex with and precipitate the drug of interest. It is possible that desmopressin (1.1 kDa, 1 cationic charge) has too low of a charge density for the experiment proposed above.

We have discussed counterion pKa and log[thin space (1/6-em)]P values independently in the previous two sections. Researchers have noted that for a given counterion, it is prudent to also consider pKa and log[thin space (1/6-em)]P together.56,65,78 Carneiro et al. noted that triethylamine was a worse hydrophobic counterion for pairing with all-trans retinoic acid than both benethamine and stearylamine. Although triethylamine is a stronger base than the other two counterions, and should therefore be able to interact more easily with retinoic acid, it is so much less hydrophobic that the resulting complex does not have the desired lipophilicity.65 Likewise, Lu et al. screened fifteen counterions as candidates to form hydrophobic complexes with the pentacationic peptide polymyxin b.78 We found that at constant counterion pKa, the threshold log[thin space (1/6-em)]P required to form an ion pair hydrophobic enough for their encapsulation method (nanoprecipitation) varied. For aliphatic fatty acid sodium salts such as sodium hexanoate, sodium decanoate, and sodium oleate, precipitates formed at counterion log[thin space (1/6-em)]P values above 4. Only sodium oleate, log[thin space (1/6-em)]P ∼ 6.8, formed complexes that precipitated as required for encapsulation (green box, Fig. 5). Sulfate surfactants formed sufficiently hydrophobic complexes at and above log[thin space (1/6-em)]P values of ∼2 (yellow box, Fig. 5), suggesting that the sulfate surfactants interact more strongly with polymyxin b's cationic charges and form an ion pair more readily than the carboxylic acids. At a counterion log[thin space (1/6-em)]P of 5, dodecylbenzene sulfate formed a sufficiently hydrophobic complex, but fatty acids decanoate and myristate did not (red box, Fig. 5).


image file: c9na00308h-f5.tif
Fig. 5 pKa and log[thin space (1/6-em)]P values for various anionic counterions. Complexes were pre-formed in MQ water at a 1[thin space (1/6-em)]:[thin space (1/6-em)]1 charge ratio with polymyxin b. Blue diamonds indicate no precipitate was observed; green circles indicate a precipitate was observed, but was insufficiently hydrophobic for nanoprecipitation; and red boxes indicate a sufficiently hydrophobic precipitate was formed. Adapted with permission from H. Lu, P. Rummaneethorn, K. Ristroph, and R. K. Prud'homme, Hydrophobic Ion Pairing of Peptide Antibiotics for Processing into Controlled Release Nanocarrier Formulations, Mol. Pharmaceutics, 2018, 15(1), 216–225. Copyright (2017) American Chemical Society.78

We recommend that researchers complex their drug of interest using a suite of counterions at first, noting the pKa and log[thin space (1/6-em)]P values of the counterions used. The resulting complex's aqueous solubility and/or lipophilicity can be measured, and counterion chemistry or charge ratio can be varied to tune these values as desired.

Complexation: pre-formed vs. in situ. Ion paired complexes may be formed either prior to or during encapsulation; we call the former a ‘pre-formed’ complex and the latter an ‘in situ’ complex. In the literature, the vast majority of complexes are pre-formed in water or a water–organic mixture, then isolated by precipitation or filtration, washed, and dried.39,49 This approach allows researchers to measure the complex's log[thin space (1/6-em)]P empirically and fully characterize it using techniques such as differential scanning calorimetry (DSC), X-ray diffraction (XRD), NMR, FTIR, etc.79 Isolated complexes are often loaded into an oil phase or organic solvent (e.g. DCM80,81 or acetone82) and treated as a lipophilic molecule. Since the oils and organics used are aprotic and often nonpolar, dissociation is unlikely.

Pre-formed complexes have a known stoichiometry and are already paired together, meaning electrostatic interactions between the drug and other delivery vehicle components are less likely to occur during encapsulation. This is particularly advantageous when encapsulation relies on charged species, such as lipid pH coacervation to encapsulate a complex. In lipid coacervation, ionized lipids are precipitated by dropping the solution pH below their pKa values.83,84 An undissolved hydrophobic pre-formed complex is less likely to ion pair with the lipids used than a dissolved, charged drug would be.

Many researchers have noted that when pre-forming at drug[thin space (1/6-em)]:[thin space (1/6-em)]surfactant charge ratios above 1[thin space (1/6-em)]:[thin space (1/6-em)]1, excess surfactants form micelles.50,85–88 A solution that is cloudy and has visible precipitates at a 1[thin space (1/6-em)]:[thin space (1/6-em)]1 charge ratio may become clear when more surfactant is added, indicating the presence of micelles that solubilize the hydrophobic complex. When the log[thin space (1/6-em)]P of these micelle-loaded complexes is measured, it is unsurprisingly lower than the complex alone.50,61 For this reason, many studies using the pre-forming approach have stayed at or near a 1[thin space (1/6-em)]:[thin space (1/6-em)]1 drug[thin space (1/6-em)]:[thin space (1/6-em)]surfactant charge ratio to avoid micelles. Using higher charge ratios (e.g. 1[thin space (1/6-em)]:[thin space (1/6-em)]2 drug[thin space (1/6-em)]:[thin space (1/6-em)]surfactant, 1[thin space (1/6-em)]:[thin space (1/6-em)]4, etc.) should not be fully ruled out, though. Drying the pre-formed complex by lyophilization should disrupt micelles and yield a complex with a stoichiometry closer to the desired charge ratio, which may be required to tune release. This will be discussed further in the following section.

In situ ion pair formation is less common but avoids the micellization problem. Ashton et al. and Song et al. successfully paired AZD2811 with anionic surfactants during their nanoemulsion's formation, and Mussi et al. added docosahexaenoic acid to the oily phase of their SLN emulsion to pair with doxorubicin in situ.38,70,89 Pinkerton et al. and Lu et al. complexed small molecule and peptide APIs with counterions during rapid mixing in nanoprecipitation.43,47,78 A comparison between pre-formed and in situ ion pairs at a 1[thin space (1/6-em)]:[thin space (1/6-em)]1 charge ratio found no appreciable difference in the size of NPs formed by nanoprecipitation.78

Charge ratio. Screening multiple drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion molar ratios is a straightforward series of experiments to perform. By doing so, researchers have measured how a number of important parameters vary with charge ratio: complexation efficiency,18,51,57,86–88,90–98 complex log[thin space (1/6-em)]P50,98–100 and zeta potential,93,101,102 drug encapsulation efficiency,30 and even droplet size in a SEDDS (self-emulsifying drug delivery system).94 Complexation efficiency in water is typically measured by centrifuging precipitated complexes and measuring the amount of free drug in the supernatant. When measured this way, efficiency is often reported as going through a maximum near a 1[thin space (1/6-em)]:[thin space (1/6-em)]1 drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion charge ratio because of the solubilization of drug into micelles at higher ratios (more counterion) and insufficient complexation at lower ratios (less counterion). We note again that at the higher charge ratios, complex formation is not less efficient than at the 1[thin space (1/6-em)]:[thin space (1/6-em)]1, but that solubilization into micelles at equilibrium results in less complex settling during centrifugation. The final solution contains solubilized drug in thermodynamically stable micelles, and a second phase which is the drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion complex with a different stoichiometry.

log[thin space (1/6-em)]P measurements as a function of charge ratio are sometimes reported to go through a maximum around 1[thin space (1/6-em)]:[thin space (1/6-em)]1 as well. This is seen particularly if the experiment conducted involved forming an ion pair in water and then adding octanol.50 At charge ratios with higher counterion concentrations, micelles will have already formed in water by the time octanol is added and will be very unlikely to partition into the octanol phase. A better experimental design is to dissolve counterions first in octanol-saturated water and then add the drug of interest,99 or to dry the pre-formed complex before adding it into an octanol–water system.86,98 In this case, log[thin space (1/6-em)]P vs. charge ratio shows asymptotic behavior at higher counterion charge ratios.

Drug release as a function of drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion charge ratio has also been reported.71,78,103 As may be expected, at charge ratios with more equivalents of counterion, the release rate of drug from delivery vehicle slows. This is likely because the complex is more hydrophobic, or slower to dissociate, or both. We will discuss this phenomenon in more detail in the following section.

3. Encapsulation techniques

A number of common encapsulation techniques have been applied to molecules during or after hydrophobic ion pairing. This section discusses specific considerations that should be made when using these techniques to encapsulate an ion paired molecule. A general overview of some processing parameters and important outcomes such as encapsulation efficiency and drug loading is provided.

Encapsulation efficiency (EE): the encapsulation efficiency for a given drug formulation is calculated by measuring the amount of free drug (i.e. not encapsulated in or associated with delivery vehicles) after complexation and encapsulation. Separating free drug from delivery vehicles may be done via ultrafiltration or centrifugation, when the free drug and delivery vehicles have very different sizes, or by a technique such as size exclusion chromatography, for separating proteins from nanoparticles where filtration is ineffective. Once the amount of free API is measured, encapsulation efficiency is reported according to the following equation:

image file: c9na00308h-t2.tif

For a formulation technique to be implemented at the industrial scale, high encapsulation efficiency – i.e. less material lost during processing – is desirable. High drug loading and few unit operations are also preferred.

Many papers report that HIP enabled researchers to encapsulate molecules that they previously could not, or that the technique improved their system's encapsulation efficiency, sometimes by more than 50%.18,49,84,87,88,90,101,104–110 Encapsulation efficiencies higher than 90%49,60,84,102,103,105,106,111 and as high as 100%57,78,82,109,112 have been reported.

Drug loading: the mass fraction of API in a nanodelivery vehicle is the drug loading. The rest of the vehicle mass consists of excipients such as lipids, stabilizing polymers, oils, etc. Using HIP, drug loadings ranging from 3–7%,85,106,112 10–20%,57,81,101 and up to 30% (ref. 47, 78 and 113) have been reported. Some formulation strategies have inherent limits on drug loading; for example, S/O/W emulsions form percolation networks when the oil phase containing a hydrophobic drug reaches too high a volume fraction within a single droplet.12 Therefore, in these systems there is an inverse relationship between drug loading and vehicle stability, which is undesirable at scale and for clinical application.

3.1 Emulsions

Single (e.g. oil-in-water, O/W)38,39,56 and double (e.g. solid-in-oil-in-water or water-in-oil-in-water, S/O/W or W/O/W),18,90,91 etc. – see Table 3 emulsions have been used to encapsulate ion paired complexes into droplets that may then be dried or otherwise further processed. Both require surfactants to stabilize, and typically a non-ionic species such as PVA is used. Using an ionic surfactant as an emulsion stabilizer may interfere with the hydrophobic complex's formation or stability.

Researchers commonly pre-form hydrophobic complexes prior to introducing them into an emulsified system. This has an advantage over in situ formation in that the complex may be added to the oil phase before emulsification, which promotes better encapsulation. If the hydrophilic component were introduced in the aqueous phase and the hydrophobic counterion were introduced via the oil phase, pairing would likely occur at oil-water interfaces if at all (and the degree of counterion ionization in the oil phase would be difficult to determine and control). If both components were added unpaired in a mixed oil phase, pairing would again be limited by ionization. Finally, if API and counterion were introduced in water and allowed to pair, the resulting hydrophobic complex would need to partition into the oil droplets, which would take longer and be less efficient than loading the pre-formed complex into oil, where it will prefer to remain.

A HIP complex's final geometry and possible amphiphilicity are another parameter that should be considered. A hydrophilic API's water-soluble charged group may be complexed by HIP, but other polar regions on the molecule may result in an amphiphilic complex that may tend to accumulate on the emulsion droplets' oil-water interface.97 Using excess counterion, or a counterion with larger hydrophobic regions, may partially mitigate this effect. Proteins may be stabilized from denaturation at oil–water interfaces may be stabilized via ion pairing if they are complexed in such a way that their tertiary structure is largely preserved and their hydrophilic regions, which would lead to interfacial aggregation if exposed, are hidden.12,100

3.2 Lipid nanoparticles

Hydrophobic complexes have been incorporated into solid lipid nanoparticles either by emulsification from a hot melt46,65,70,105,107,108,114,115 or by stearic acid coacervation.83,84,116 In the former, non-ionic lipids and surfactants such as glyceryl behenate were heated and added to an oil phase along with a pre-formed complex. The hot oily phase was added to water and sonicated. With no other charged species present, it is unlikely that the ion pair was disrupted prior to encapsulation. Carneiro et al. note that without complexation, the API of interest, all-trans retinoic acid, resides primarily at the lipid–water interface, and that hydrophobic complexation helps incorporate it more fully in the lipid matrix.65

Lipid nanoparticle formation by stearic acid coacervation involves lowering the pH of a solution of water and ethanol containing stearic acid to protonate and precipitate it as a free acid.83,84,116 In these systems, a pre-formed hydrophobic complex was added along with ethanol into the hot aqueous solution of stearic acid. Since ion pair formation and stability vary with ionic strength and pH, it remains unknown if the ion pair remained together during this formulation strategy, or if dissociation (and possibly re-pairing between the drug and stearic acid, before the pH dropped too low) occurred. Therefore the final stoichiometry and identity of the ion pair are difficult to know, even using a pre-formed system in the presence of additional potential ion pairing partners.

3.3 Precipitation

Controlled nanoprecipitation techniques such as Flash NanoPrecipitation take advantage of diffusion-limited aggregation between precipitating molecules in an aqueous or mixed solvent system. Hydrophobic complexes are well-suited for this approach, since their water solubility is very poor and they precipitate quickly. Rapid precipitation followed by stabilization, e.g. surface deposition of the hydrophobic block of a block copolymer, yields kinetically trapped core–shell nanoparticles.47 Rapid, good mixing will result in homogeneous nucleation and growth, which is desirable in nanoprecipitation. Heterogeneous nucleation or poor mixing may allow sufficient time for the formation of a thermodynamically favoured micelle phase from excess hydrophobic counterion. This is undesirable because the hydrophobic polymers or polymer blocks used in nanoprecipitation may not deposit onto a micelle's charged surface as they would onto a hydrophobic surface, and the same kinetically-trapped particle may not be formed.

Researchers have demonstrated both in situ and pre-formed ion pairing approaches with nanoprecipitation. Water is typically used as an antisolvent to induce precipitation, so using salt forms of the API is a straightforward method of ensuring an initially ionized state of the API. This means that in situ complex formation, followed immediately by precipitation, is easy to accomplish. Unlike the water–oil systems such as those used for emulsions, nanoprecipitation systems use water-miscible organic solvents, meaning interfacial partitioning is not a factor. The main limit to complexation is therefore diffusion, falling in line with nanoprecipitation's typical diffusion-limited aggregation kinetics. Lu et al. reported that even in a Flash NanoPrecipitation system, where rapid mixing on the order of 2 ms is followed by nucleation, growth, and stabilization by block copolymer adsorption all within about 20 ms, complexes formed in situ were efficiently encapsulated.43,78 This suggests the time scale of complexation and precipitation is less than 20 ms. This is comparable to the precipitation time of a strongly hydrophobic (log[thin space (1/6-em)]P > 5) molecule – or pre-formed hydrophobic complex – in the same system.

Precipitation with a compressed antisolvent (PCA) has also been used to encapsulate HIP complexes into nanoparticles or microparticles.82,117–119 Because the mixing in PCA is between a solvent containing the drug of interest and a chamber of pressurized gas, pre-formation of the hydrophobic complex is required.

3.4 Others

Other formulation strategies can be viewed through a similar lens to the one we have used above. Techniques that treat a pre-formed complex such as a typical hydrophobic molecule are valid provided they have not neglected the complex's sensitivity to salts and pH. For example, self (micro/nano)-emulsifying drug delivery systems (S[M/N]EDDS) may use either ionic or non-ionic surfactants. We described when discussing lipid nanoparticles that ionic surfactants could disrupt ion pairing or exchange with a complex's counterions – these considerations are important to keep in mind when modifying a system usually used to encapsulate a non-ionic hydrophobic molecule to one capable of encapsulating a HIP complex.

Systems that require pH modulation are not wholly ineligible for use with HIP, but care should be taken to ensure that the complex is not disrupted if possible. Consider Iqbal et al., who used a unique method of interpolymer complexation between polyethylene glycol and poly(acrylic acid) to form nanoparticles.11 This required adjusting the solution pH to 3 to protonate poly(acrylic acid); the cationic drug of interest was pre-formed with docusate and introduced along with Pluronic F68 in ethanol into an acidic aqueous PAA solution. Docusate has a sulfonate head group that should remain charged at pH 3, and PAA was already protonated and uncharged before the complex was added. Taken together, these suggest the pre-formed leuprolide:docusate complex was likely to survive intact in this formulation technique than in (1) one where it encountered another ionized species (as in the case of stearic acid coacervation discussed above) or (2) a system using a hydrophobic counterion (e.g. a fatty acid) that would be deprotonated at the final pH.

4. Ion paired drug release from a delivery vehicle

Drug release from a delivery vehicle containing a hydrophobic complex varies with the type of vehicle (core–shell nanoparticle, SLN, double emulsion, SEDDS, etc.), but useful similarities exist. The ion paired drug will behave like a hydrophobic molecule as long as it remains complexed. Once complexation is reversed, the original hydrophilic molecule and hydrophobic counterion are regenerated and will usually partition out of the delivery vehicle. De-complexation is driven by one of two main mechanisms: counterion competition by salts or pH-driven charge negation. The former occurs when salts in the surrounding medium are able to access the complex and outcompete the hydrophobic ion pair, leading to dissociation. The high ionic strength in the surrounding medium screens the charges between the two regenerated species, so re-complexation is unlikely. The former follows a similar mechanism, protonating or deprotonating one of the charged species and leading to de-complexation.

Both mechanisms depend on water accessing the hydrophobic complex. For this reason, the vehicle's type and geometry are both important. Core–shell nanoparticles have a less water-accessible core than PLGA-stabilized double emulsions, for example, and it may be expected that they release drugs more slowly in similar salt/pH conditions. Because water can access ion pairs at the water–vehicle interface much more readily than complexes deep in the vehicle core, release is expected to occur from the outside in. After ion pairs at the surface have been de-complexed and partition into the bulk phase, water will be able to access the complexes deeper in the vehicle. During this ‘erosion,’ the vehicle itself may lose structural integrity or collapse.61 For vehicles with low drug loading, the hydrophobic complex's location in the vehicle is another factor to consider. A complex with amphiphilic character that resides primarily on the vehicle surface is easily water-accessible, and rapid burst release may be observed.65,97,111

The fact that de-complexation is a precursor to this type of release explains why slower drug release is seen at higher charge ratios.71,78,103 A monovalent drug complexed with a single monovalent counterion should fully dissociate much more quickly than a drug complexed with four, and will not release from the vehicle until it is fully dissociated. In the 1[thin space (1/6-em)]:[thin space (1/6-em)]4 charge ratio case, only one of the counterions can truly form an ion pair with the drug (see the preceding section on drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion charge ratio). The remaining three counterions can remain associated with the complex, though, adsorbing onto the first counterion via tail–tail hydrophobic interactions. The resulting large hydrophobic surface area serves as a mass transfer barrier that slows water diffusion to the site of ion pairing. For this reason, it is more difficult for water to access and dissociate the 1[thin space (1/6-em)]:[thin space (1/6-em)]4 complex than the 1[thin space (1/6-em)]:[thin space (1/6-em)]1 complex, so drug release is slower. The probability of a drug re-complexing with a hydrophobic counterion after salt-driven decomplexation also increases with the number of hydrophobic counterions near a drug molecule.

After dissociation, the therapeutic and counterion are regenerated. Without its hydrophobic counterion, the therapeutic is likely too hydrophilic to remain associated with the vehicle (even if the solution pH has turned off the drug's charge) and will partition into the bulk. Depending on its chemistry and the bulk pH, the counterion may either diffuse into the bulk or remain with the vehicle. For example, we found that at a 1[thin space (1/6-em)]:[thin space (1/6-em)]4 polymyxin B[thin space (1/6-em)]:[thin space (1/6-em)]oleate charge ratio, drug release plateaued around 35%. This suggests that after soluble polymyxin b was released, the poorly-water-soluble oleate fatty acids remain with the nanoparticle and may form an oleate/oleic acid liquid crystal phase in or around the NP core. This type of plateauing release profile was not observed for polymyxin paired at a 1[thin space (1/6-em)]:[thin space (1/6-em)]4 polymyxin[thin space (1/6-em)]:[thin space (1/6-em)]SDS charge ratio, because SDS is more water-soluble and prefers to partition into the bulk.78

Complexation formation, dissociation, and release have all been found to be a function of bulk ionic strength.18,38,44,45,72,120 As expected, at higher ionic strength, it is more difficult to form complexes due to charge screening, and, if formed, complexes dissociate and drugs are released faster at higher salt concentrations. PBS, sodium chloride, and serum are common release media. Researchers have found both complexation18,57,120,121 and release30,38,48,70–72,105,112,121 to be pH-dependent. These assays are usually run at pH values at and below 7.3. In most cases, faster release at lower pH has been observed as expected.

This understanding of the mechanism behind salt- and pH-dependent release is useful. Many nano-scale delivery vehicles are stable in water and can be stored in deionized water without beginning to release their payload. For parenteral or oral formulations, the body's natural ionic strength will trigger release. pH-dependent release could be useful for targeting to endosomes, tumors, or different regions in the intestinal tract. On the other hand, pH sensitivity may rule out some long-term depot delivery strategies; for example, it has been well-documented that PLGA microparticles may acidify as the polymer is degraded over time.12,122 An acid microenvironment could trigger ion pair dissociation and lead to faster release.

The previous several paragraphs have discussed drug release following ion pair dissociation. In general, unless a hydrophobic complex is exposed to salts or pH changes, it should behave like a hydrophobic molecule – depending on the vehicle and the chemistry of the species that make up the pair, the complex could still be released intact from the vehicle. Hydrophobic molecules in nano-scale delivery vehicles can diffuse and, depending on their solubility in the release medium, may still partition into the bulk. The complex's size and hydrophobic interactions with the delivery vehicle are barriers to diffusion.65,66,116 When buffers containing only salts are used as simple release media, this type of release is unlikely. In more complex, more realistic release media – i.e. those containing some kind of hydrophobic sink such as albumins or bile salt micelles – this type of direct release, as well as salt- or pH-driven release, may occur simultaneously. The driving forces for diffusion of all species, including paired and unpaired drugs and paired, unpaired, and uncharged counterions, should be considered.

It is straightforward to see that both major exit routes from a particle – either following dissociation or as an intact complex – depend on the complex itself and the counterion used. Alkyl tail length or hydrophobic group size, for example, affect both. In the case of post-dissociation release, larger hydrophobic surface areas decrease water permeability and slow decomplexation, as discussed in the paragraph about release as a function of charge ratio. And in the case of release as an intact complex, longer alkyl tails both decrease the complex's solubility in the bulk and increase steric and hydrophobic interactions that tend to keep the complex in its vehicle. As counterion hydrophobicity increases, therefore, release tends to decrease (Fig. 6).29,38,65,78,88


image file: c9na00308h-f6.tif
Fig. 6 A summary of how complexed drugs may be released from a delivery vehicle. (A) The intact complex may release directly from the particle into the bulk. This type of release is a function of the complex's solubility in the bulk, so hydrophobic sinks such as bile salt micelles or albumins in the bulk phase will provide more of a driving force than simply a buffer. (B) Salts lead to counterion competition and decomplexation, which is followed by release as the water-soluble drug is released into the bulk. (C) When counterions such as fatty acids are used, lowering the pH below their pKa will lead to protonation. The protonated counterions will no longer complex the drug, leading to release as in (B).

5. Bridging polyelectrolyte coacervation, polymer–surfactant complexation, and hydrophobic ion pairing

The HIP literature has generally not overlapped with the literature from the fields of polyelectrolyte–polyelectrolyte coacervation or polyelectrolyte-surfactant complexation. The fields share a number of similarities that we will highlight here. Polyelectrolyte complex coacervation used here refers to the phase separation induced when oppositely-charged polyelectrolytes or ionomers ion pair with one another, and is not to be confused with the acid-induced lipid precipitation technique mentioned earlier (which is also called ‘coacervation’). Polyelectrolyte-surfactant complexation has been studied extensively and is useful in a number of industrial applications, including personal care products and detergents.123

5.1 Polyelectrolyte coacervation

Ion pairing between polyelectrolyte species results in the formation of a highly electrostatically crosslinked complex that phase separates from its surrounding media; the new phase may be either a solid (‘precipitate’) or liquid (‘coacervate’), but the term ‘complex coacervation’ is applied in both cases.124–126 Stoichiometric ratios (i.e. 1[thin space (1/6-em)]:[thin space (1/6-em)]1 cation[thin space (1/6-em)]:[thin space (1/6-em)]anion) are common in this literature, since these systems tend to form more distinct coacervate phases from charge neutral conditions – at uneven ratios, electrostatically-stabilized colloidal particles may form.125 Like hydrophobic ion pairs, coacervate phases are sensitive to salt and may be dissociated at sufficient ionic strength or as a function of pH, depending on the chemistry.

The entropic and enthalpic effects of coacervate formation and phase separation have been studied and reported elsewhere.125,127–132 Interestingly, polymers in a complex coacervate may remain mobile, and rearrangement is possible. Many studies focus on the coacervate's phase behaviour133 or rheological134 or thermal135 properties. The final phase's log[thin space (1/6-em)]P (and hydrophobicity in general) is not a major concern in complex coacervation, since the mechanism of phase separation is different and the ultimate goal of coacervation is not necessarily to increase hydrophobicity or modify solubility as in HIP.

Because complex coacervates form distinct phases, the technique has been studied as a possible method of encapsulating polyvalent drugs such as peptides and proteins.136–139 For insufficiently charged proteins, ‘supercharging’ – adding more charged amino acids – increases charge density and can lead to more reliable coacervation.140 Some similarities and differences between encapsulation using coacervation and HIP may be seen. Encapsulation via coacervation is typically carried out near or at a stoichiometric charge ratio.136,138 This differs from the HIP literature, where a screen of different drug[thin space (1/6-em)]:[thin space (1/6-em)]counterion charge ratios is commonly performed and the resulting complex's log[thin space (1/6-em)]P is characterized. Using a complex coacervate as a delivery vehicle introduces problems similar to W/O/W double emulsions; namely, a tradeoff between drug loading and encapsulation efficiency.141 Another notable difference between HIP and PE coacervation other than the molecular weights of the species used is the lack of ionic crosslinking in much of the HIP literature. Most HIP studies use monovalent small molecule counterions (exceptions are discussed in the following paragraph), but PE coacervation depends on polyvalency to form its characteristic crosslinked polymer networks.

Some papers using small-molecule surfactants for HIP have also used polyvalent counterions to complex drugs, and most unfortunately fail to make the distinction between the two techniques in their descriptions of what was done. The most common polyvalent counterion in these cases is dextran sulfate, a polyanionic sugar that does not contain distinct hydrophobic domains.59,91,92,104,120 When it is used to complex multivalent APIs such as proteins, dextran sulfate forms a complex coacervate rather than a true hydrophobic ion pair. The coacervate may still be encapsulated using methods that also encapsulate hydrophobic ion pairs, but drug release from ion pairs compared to coacervates may differ noticeably. Consider Song et al., who found that drug release of an ion paired multivalent small molecule AZD2811 varied significantly whether using pamoic acid (divalent) or xinafoic acid (monovalent, effectively half of pamoic acid) at the same charge ratio.38 The difference in release profile observed was most likely a function of crosslinking between divalent pamoic acid and the multivalent small molecule, which resulted in slower release. It is easy to see that a system containing dextran sulfate, which has much greater protein crosslinking potential than divalent pamoic acid, could be expected to have very different release kinetics from a system using a small molecule surfactant counterion. Understanding and carefully distinguishing between the two approaches will be beneficial for future studies aiming to ionically complex and encapsulate charged therapeutics.

5.2 Polymer–surfactant complexation

Polymer–surfactant complexation and phase behavior have been studied for decades.142,143 The field has carefully examined precipitate formation as a function of many parameters familiar to the hydrophobic ion pairing literature, including charge density,144 stoichiometry, and formation and dissociation in the presence of salts.145 Studies of self-assembly have developed binding isotherms and a thermodynamic understanding of surfactant monolayer and bilayer formation.123,146,147 Important questions in this field include: what are the phase behavior and rheological properties (surface tension, viscosity, etc.) of polymer–surfactant complexes?144,148,149 Do they form one-phase or two-phase systems, and does this change upon dilution – i.e., what are the critical aggregation concentrations? What is the effect of surfactant alkyl tail length on this behavior?146,150 Are the polymers binding to surfactant monomers, or micelles?145,151

The polymers used in these studies often have higher molecular weight and more regular charge spacing than the peptides and proteins complexed with surfactants in the HIP literature. As in the coacervation literature, imparting additional hydrophobicity to a polymer is not necessarily the ultimate goal of a study, and drug encapsulation is rarely discussed. These studies often examine wetting or solubilization behavior, and are useful in the development of new detergents and shampoos.

A familiarity with the field of polyelectrolyte-surfactant complexation will help hydrophobic ion pairing researchers appreciate similar sensitivities – e.g. to salts, temperature, or pH – that their own systems might experience. It will also help them develop an appreciation for surfactant phase behavior, which has not been well-characterized in most studies that use HIP to encapsulate a drug molecule.

6. Perspective

Encapsulating hydrophilic therapeutics via hydrophobic ion pairing is a useful technique and offers a number of attractive possibilities. In this section, we highlight four major ones: (1) co-encapsulating hydrophilic and hydrophobic drugs, (2) forming a HIP complex from two therapeutic species, (3) decreasing API crystallinity, and (4) tuning drug release rates by simply altering the counterion used in HIP.

Many encapsulation techniques that have been optimized for hydrophobic therapeutics can easily be adapted to work on ion paired hydrophobic complexes. This introduces a unique and powerful possibility: straightforward co-encapsulation of hydrophilic and hydrophobic therapeutics into a single delivery vehicle at high loadings. This is highly desirable, and is not possible using encapsulation techniques developed specifically for water-soluble drugs, e.g. W/O/W emulsions. Using two different encapsulation techniques to prepare two populations of particles encapsulating two therapeutics can be difficult (and expensive), especially if the particle chemistries, sizes, and fates are intended to match. There can be no guarantee of simultaneous delivery or even co-delivery in the body using a mixed population of particles, particularly at the single-cell level where local concentrations of both species may be important for therapeutic synergy.

Using HIP, researchers have co-encapsulated hydrophilic and hydrophobic therapeutics.30,71,103 Tuning release rates of co-encapsulated drugs from these two classes is an exciting prospect for future study. For example, Zhou et al. found their hydrophobic therapeutic released at a pH-independent rate, while the ion paired complex's release varied with pH.30 Future formulations may take advantage of this difference in behaviour while still benefiting from co-localization. Or, if the mismatch is undesirable, researchers could tune parameters discussed above such as charge ratio, counterion chemistry, etc. to make hydrophilic and hydrophobic release rates match.

Another exciting opportunity of hydrophobic ion pairing is the co-delivery of two water-soluble charged APIs by ion pairing the two of them together. Denadai et al. formed a hydrophobic complex from two therapeutic small molecules, cationic chlorhexidine and anionic losartan, but did not encapsulate the result in a separate delivery vehicle.152 Other papers report choosing their counterion based on therapeutic synergy. Kalhapure et al. chose from among several similarly-lipophilic counterions – palmitoleic, oleic, linoleic, linolenic, and arachidonic acid – by checking the ability of each to inhibit S. aureus growth. Linoleic acid's MIC was superior to the others, so it was used to pair with vancomycin.64 Similarly Oliveira et al. ion paired doxorubicin with α-tocopherol succinate to take advantage of the anticancer properties of each,105 and Li et al. paired doxorubicin with hyaluronic acid since the latter is possibly useful for tumor targeting.153

Several papers have reported that ionic complexation with hydrophobic counterions formed an ion pair with lower crystallinity than its individual components.28–30,43,46,47,154 Improved amorphous character may be useful for quickly releasing drugs, particularly as intact complexes, if desired. It may also be helpful for formulating hydrophobic ionic drugs into stable NPs with faster dissolution kinetics.43 In this case, controls with a non-ionic analogue of the counterion (e.g. methyl esters instead of carboxylic acids; see Oliviera and Mussi for examples of this important control experiment) should be used to determine if reduced crystallinity is simply a co-core confinement effect or truly the result of HIP.70,105

For formulations containing a HIP complex, tuning drug release rates by changing the hydrophobic counterion or API[thin space (1/6-em)]:[thin space (1/6-em)]counterion charge ratio used is a straightforward and powerful tool for formulation scientists and drug delivery researchers.71,78,103 Changing the amount or type of counterion used during a formulation technique while holding all other excipients and processing steps constant is relatively easy and should allow for several formulations with different release rates – and therefore possibly different PK profiles – to be developed and tested in rapid succession.

Hydrophobic ion pairing remains an active area of research, and several fundamental aspects of the process remain unclear: the precise dynamics of API–counterion assembly, aggregation/precipitation, and dissociation/release as a function of drug and surfactant chemistry (e.g. head group/pKa, charge density, charge ratio, pH, ionic strength, hydrophobic moieties, etc.) are active areas of research. The phase behavior of surfactants used as hydrophobic counterions once paired is similarly unknown; this may prove to be an important parameter in modulating release.78 Molecular dynamics simulations may be the best way to examine the details of these phenomena, as they have been used extensively to study PE coacervation and PE-surfactant complexation.130,131

We have reviewed how and why drug release from an ion paired system varies with counterion. It remains unknown if a mixture of counterions in a single formulation could lead to two different release profiles simultaneously; e.g. preparing two different pre-formed complexes of a cationic peptide with two different anionic surfactants, then incorporating both into a single formulation to achieve an initial burst release followed by slower, steady release over time.

This review has summarized the many proof-of-concept studies that demonstrate hydrophobic ion pairing as a useful tool for complexing and encapsulating hydrophilic therapeutics across several classes – small molecules, peptides, protein fragments, and full proteins such as antibodies and enzymes – into nano-scale delivery vehicles. The technique is straightforward, uses accessible and inexpensive surfactants, and yields hydrophobic complexes that may be precipitated, emulsified, or otherwise packaged using existing technology. Fundamental questions remain about counterion phase behavior, the details of hydrophobic and ionic interactions during complexation, and the exact mechanism of drug release across several chemistries and external parameters. Moving forward, the field offers exciting possibilities such as co-encapsulation of hydrophobic and hydrophilic therapeutics, collaborations with the related fields of polyelectrolyte coacervation and polyelectrolyte-surfactant complexation, or the co-encapsulation and co-delivery of two ionic APIs by forming a HIP complex from the two of them.

Abbreviations

a prioriBeforehand
APIActive pharmaceutical ingredient
ceteris paribusWith all else being equal
CTABCetrimonium bromide
DCMDichloromethane
DSCDifferential scanning calorimetry
et al.And the others
FDAUnited States Food and Drug Administration
FTIRFourier-transform infrared spectroscopy
HIPHydrophobic ion pair/pairing
in situon site/in place
IPIon pair or ion pairing agent
NMRNuclear magnetic resonance
N/P ratioMolar ratio of cationic nitrogen in lipids to anionic phosphorous in nucleic acids, used in the lipoplex literature
NCsNanocarriers
NPsNanoparticles
PBSPhosphate-buffered saline
PLGAPoly(lactic-co-glycolic acid)
SDSSodium dodecyl sulfate
SLNSolid lipid nanoparticle
S(M/N)EDDSSelf-(micro/nano)emulsifying drug delivery system
XRDX-ray diffraction

Funding

We acknowledge financial support from the Bill and Melinda Gates Foundation (BMGF OPP1150755), The Princeton SEAS Helen Shipley Hunt Fund, and the National Science Foundation for the research fellowship for K. D. R. (DGE-1656466) and (CBET 1605816).

Conflicts of interest

There are no conflicts to declare.

Acknowledgements

The authors thank Dr Nathalie Pinkerton, Dr Robert Pagels, Mr Chester Markwalter, and Mr Douglas Scott for intellectual discussion and for their help reviewing the document.

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