Introduction

Liposomes or lipid nanoparticles (LNPs) are the self-assemblies of lipids in aqueous environment, and the presence of hydrophobic and hydrophilic regions makes them ideal candidates for the encapsulation of a variety of therapeutic molecules [1,2,3,4,5,6,7,8,9]. However, liposomes are susceptible to leakage and aggregation because of hydrolysis and oxidation of lipids [10], and therefore, the physical stability of liposomes becomes an important consideration for their applications as drug carriers [11, 12] and vaccines [13,14,15]. The hydrophilic headgroup and the hydrophobic acyl chain length of the constituent lipids determine the overall packing behavior, surface charge, and the interfacial stability of the liposomes or lipid nanoparticles (LNPs) [16, 17]. The packing parameter (P) of the constituent lipids is defined as

$$P = \frac{V}{{SL_{{\text{C}}} }}$$
(1)

where V is the hydrophobic volume, S is the surface area of the occupied by the polar region, and Lc is the extended length of the hydrophobic tail chain[18,19,20]. Therefore, the choice of the constituting lipid governs the thermal stability owing to the melting, and other temperature-dependent characteristics of the lipids which attributes to the leakiness of the lipid bilayer. Lipid membrane leakage is undesirable because it decreases the efficacy and shelf life of liposomes [21,22,23]. An approach to overcome this leakage is to modify the acyl tails by introducing light-sensitive polymerizable moieties [24,25,26]. The cross-linked acyl tails in the presence of light of a suitable wavelength changes conformation to release the contents in the organ of interest [27, 28]. In the absence of the light, the links in the acyl chain do not change conformation and prevent the leakage of contents [29, 30]. Furthermore, steric stabilization or prevention of aggregation can be induced by introducing polymers and block co-polymers such as polyethylene glycol (PEG), polyvinyl alcohol (PVA) [31, 32], polylactic acid (PLA) [33, 34], and polyglycolic acid (PGA) polymers [35,36,37,38] on the liposome surface and the outer lipid leaflet. Amongst these, only PEG polymer has shown an efficient and lasting steric stabilization which is also approved by the FDA [36, 38, 39].

DC8,9PC [1,2-bis(10,12-tricosadiynoyl)-sn-glycero-3-phosphocholine] is photopolymerizable lipid consisting of polymerizable diacetylene linked to the tail chains [40] that results in tubule-like self-assemblies in an aqueous environment [41, 42]. However, when present in the presence of matrix phospholipids such as DPPC or other polymeric lipids like DSPE-PEG, DC8,9PC forms vesicle-like structures. The diacetylene bonds present in the tail chains of the vesicles or liposomes upon photoactivation changes conformation (from cis to trans) to release the encapsulated content to the target location [29, 43,44,45,46]. Our recent work involving PEGylated-DSPE lipids along with DC8,9PC, resulted in formation of stable vesicular lipid nanoparticles (LNP’s) in the nanometer size range of 99–110 nm [47]. This unique lipid packing was found to be dependent on the mole ratios of the pegylated lipids (DSPE-PEG), with optimal concentrations of up to 20 mol%. The LNP’s composed of this polymeric, DC8,9PC along with DSPE-PEG2000 successfully encapsulated of the photodynamic therapy (PDT) drug, 2-[1-hexyloxyethyl]-2-devinyl pyropheophorbide-a (HPPH), a well-known hydrophobic photosensitizer at relatively high concentrations. These liposomal carriers and HPPH demonstrated faster skin clearance and deeper tumor penetration at lower dosage rates as opposed to various other FDA approved photosensitizers [48,49,50] in addition to their stability at room temperatures. The HPPH-loaded LNPs exhibited remarkable PDT efficiency and animal survival rates during the clinical trials [47], with potential biomedical applications in enhanced drug delivery [47, 51].

Sterically, the inclusion of hydrophilicity through PEGylated lipids in LNPs induces stealth protection and stabilization preventing the attachment of macromolecules from the blood stream, thereby resisting phagocytosis [52,53,54,55,56]. PEGylation also increases the packing order in the headgroup and the bilayer region [57,58,59,60]. It is also assumed that PEG molecules attract water and subsequently form a steric barrier against the adherence of other macromolecules [61,62,63]. The PEGylated lipids usually assume mainly two conformations namely mushroom and brushes within the lipid bilayer based on their density. At lower PEG concentrations, the lipid head groups do not interact and follow random configurations, described as mushroom configurations. In contrast at high concentrations of PEG lipids, the surface-associated mushrooms begin to overlap and transitions to brush conformations which results in expansion of membrane area due to the lateral pressure exerted by the brush conformations [8, 64,65,66].

Differential scanning calorimetry (DSC) has been extensively used to study the thermal transitions in a lipid bilayer or the fluidity along with gaining insights on the effects of encapsulation, thermal stability and stresses of the liposomes undergoing temperature variations, particularly under the localized heating environment created during photoactivation of liposomes [67,68,69,70,71]. The presence of encapsulated material in the bilayer region is detected by DSC via formation of domains and changes in the shape of the melting peak such as broadening, temperature shifts [72,73,74,75]; and the thermal stresses are observed via annealing of the liposomal formulations through multiple heating and cooling cycles at a wide range of temperature [1, 2, 5, 76].

In this study, we investigated the steric and thermal stabilization effects exerted by the varying concentrations and molecular mass of DSPE-PEG lipid in DC8, 9PC lipid matrix. An extensive thermal analysis of the liposomal formulation demonstrated phase changes and segregation within the lipid bilayer due to the presence of encapsulated HPPH molecules. Additionally, correlations between theoretical quantified thermotropic properties such as enthalpy (ΔH) and transition temperature (Tm) with regard to thermal stability of the formulations are presented. The novelty of this fundamental work lies in filling the gap in understanding of the effects of size and concentration of PEGylated lipid DSPE-PEG in a lipid bilayer matrix comprising of a photopolymerizable lipid DC8, 9PC. The findings of this work will enable in photo-polymerizable liposomal formulation or lipid nanoparticles for potential photodynamic therapies.

Experimental

LNP formulations

Materials used

The lipids used in this study were purchased from Avanti Polar Lipids- DC8,9PC (1,2-bis(10,12-tricosadiynoyl))-sn-glycero-3-phosphocholine (cat# 870,016); DSPE-PEG1000 (1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy(polyethylene glycol)-1000] (ammonium salt), cat# 880,720); DSPE-PEG2000 (1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy(polyethylene glycol)-2000] (ammonium salt), cat # DSPE-PEG2000)); DSPE-PEG5000 (1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy(polyethylene glycol)-5000] (ammonium salt), cat # 880,220). HPPH (2-[1-hexyloxyethyl]-2-devinyl pyropheophorbide-a) was synthesized by Dr. Gary Pauly (Chemistry Core, Chemical Biology laboratory, CCR). HEPES-buffered saline (HBS) buffer of pH 7.4 of reagent grade was used.

Preparation and characterization of LNP’s

LNPs were synthesized using thin-film hydration technique. Briefly, calculated volumes of DSPE-PEG and DC8,9PC lipids suspended in chloroform were added in glass tubes to obtain the desired concentration of LNPs. The lipid mixtures were dried under a gentle stream of ultra-high pure (UHP) nitrogen gas to evaporate chloroform, that leaves a thin film of lipids in the bottom of the tubes. The dried films were hydrated with HBS buffer of pH 7.4. For the HPPH-encapsulated LNPs, HPPH solution (in DMSO) were added to the lipid mixtures prior to making the films. LNPs were prepared at 5 mg total lipid/mL in HBS, pH 7.4. Lipid suspensions were subjected to at least 5 freeze–thaw cycles and sonicated using a Probe sonicator (Branson Sonifier, Microtip probe, Fisher Scientific; 5–10 cycles, 1 min per cycle followed by 1 min of rest) using an ice bath. Upon rehydration, LNPs were uniformly sized by extruding through polycarbonate membrane of pore size 100 nm. Unincorporated HPPH was removed by low-speed centrifugation, and LNPs in the supernatant were analyzed by dynamic light scattering (DLS). Details of various formulations are provided in Table 1. The concentration of HPPH was decided based on previously performed in vivo studies.

Table 1 Composition of the lipid nanoparticle formulations used in this research (mass ratio)
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Dynamic light scattering (DLS)

Liposomal formulations containing PEGylated lipids and DC8, 9PC were suspended by probe sonication and diluted in HBS at either 1:20 or 1:40 (v/v) ratios. The size, polydispersity index (PDI) and surface charge of both encapsulated and unencapsulated liposomes were analyzed using a Malvern Instruments Zetasizer by dynamic light scattering method at 25 °C and at 173° backscatter angle with 120 s equilibration time for three technical duplicates.

Differential scanning calorimetry (DSC)

DSC studies were performed on a TA Instruments Q-2000 DSC. 10 µL of the sample were placed in T-zero Hermetic pan and sealed using DSC sample press. The samples were scanned from 25 to 75ºC at a heating rate of 10°C min−1 in an inert UHP nitrogen environment maintained at a flowrate of 40 mL min−1. The results were duplicated for reproducibility.

Results and discussion

Size and surface charge of the LNPs

Figure 1 summarizes the average particle hydrodynamic diameters and corresponding polydispersity indices (PDI) of the LNPs with (a) and without (b) encapsulated HPPH enlisted in Table 1.

Fig. 1
figure 1

Size and PDI of a LNP formulations prepared without HPPH. b LNP formulations prepared in the presence of HPPH (20:1, lipid: HPPH)

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DC8, 9PC lipids have reported to form larger tubular structures in aqueous solutions which is consistent with the large particle size of 1580 ± 30 nm with a PDI > 1[29, 47]. In the presence of PEGylated DSPE, the measured diameter of the resultant DC8, 9PC lipids LNPs dramatically reduced from 1580 nm to the range of 50 to 110 nm with lower PDIs between 0.2 and 0.45. This 93–96% reduction is size and induced uniformity in the particle diameters is attributed to the inclusion of DSPE-PEG in the tubular DC8, 9PC bilayer. Owing to its large hydrophilic head group, DSPE-PEG, induces curvature in the tubular morphology at smaller concentrations. Upon increasing the concentration of DSPE-PEG, the curvature of outer layer of the tubular bilayer changes further resulting in a favorable vesicular transformation [61, 77,78,79]. It is also observed that the formulations with 10 mol% DSPE-PEG in the case of 1 K and 5 K DSPE- PEG, and 10 mol% and 20 mol% DSPE-PEG2K are found to be uniformly monodispersed and within the acceptable nano-carrier size range of 70–200 nm and, therefore [80, 81], used to encapsulate hydrophobic drug HPPH. Figure 1b represents the change in hydrodynamic diameter and PDI of the selected formulations. The encapsulation of hydrophobic HPPH was seen to further reduce the average diameter of the LNPs representing an overall 5–15% in size reduction at lower PDIs of 0.2. This is attributed to the tighter packing of the lipids induced by the presence of HPPH which arises from intermolecular bond formations between the donor hydrogen electrons in the porphyrin ring of HPPH molecules and acceptor oxygen atoms on the glycerol moiety in the lipids. An in-depth mechanistic study of the influence of varying concentration of HPPH in the lipid bilayer is warranted and being investigated. Previous studies indicate that higher concentrations of HPPH molecules in the bilayer result in tighter lipid packing and consequently increase the stability of the lipid bilayer [61, 77, 82, 83]

Thermal analysis of the LNPs

The influence of concentrations and molecular mass of PEG polymers, and the presence of hydrophobic HPPH on the lipid segregation that leads to phase separation and domain formation in the lipid bilayer was observed by DSC. Correlations between theoretically calculated thermodynamic parameters and stability of the formulations were based on analysis of the melting curve of the lipids. The melting temperatures of pure DC8,9PC are 45 °C, pure DSPE-PEG dispersions (irrespective of molecular weight) was 52 °C and porphyrin photosensitizers degrade around 200–300 °C [84,85,86].

Effect of lower molecular weight DSPE-PEG (1000 and 2000) on phase transitions of DC 8,9 PC/PEG- DSPE LNPs without HPPH

Figure 2a shows a distinct shift of the main melting transiting peak of DC8,9PC toward lower temperature with increased concentration of PEG-2000 DSPE lipids. Pure DC8, 9PC liposomes show a melting peak (Tm) at 45° C with a small pretransition peak around 38 °C (shown in black) which is reported to occur due to the melting of the characteristic tubular microstructures of DC8, 9PC that are formed at lower temperatures [87]. These larger microtubular structure were confirmed to have an average diameter of 1580 ± 30 nm in Fig. 1a. In the presence of 1 mol% of DSPE-PEG2000 lipid (red), no significant change was observed except a slight broadening of the melting peak compared to pure DC8, 9 PC. However, at 5 mol% DSPE-PEG2000, a tall and sharp melting peak owing to larger heat capacity was observed at 43.97 ± 0.92 °C with disappearance of the pretransition peak. Upon further increasing the DSPE-PEG2000 concentration to 10 mol%, the main transition peak broadened and shifted left to 42.87 ± 0.56 °C. With subsequent addition of DSPE-PEG2000 at 20 and 50 mol%, the main transition peak began to diminish while shifting toward lower temperature. The DSC curves for the corresponding formulations in the week 4 in Fig. 2b showed similar trends, however, with reduced prominence of the melting peak. We also observed that at the end of 4 weeks (Fig. 2b.), except for formulations 2 K (5) and 2 K (10) while all the other LNPs were devoid of significant enthalpies of transition. As indicated earlier, the broadening of the melting peak, phase separated, melting domain formation and any other change observed in the shape of the melting peak correlates to the changes in the lipid bilayer due to surface binding or the presence of moieties in the bilayer region. Herein, theoretical quantification of the changes in melting peak due to presence of therapeutic foreign molecules such as HPPH in this work and the effect of their cooperativity on lipid bilayer is computed as enthalpy and the half-width of melting peak as summarized in Table 2. The thermodynamic properties associated with the melting peaks observed in Fig. 1a, b are also enlisted in Table 2.

Fig. 2
figure 2

DSC curves of DC8, 9PC/DSPE-PEG 2000 LNPs with varying PEG concentrations recorded in a) week 1 and b) week 4

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Table 2 Calculated thermodynamic parameters based on melting peaks presented in Fig. 2
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Addition of DSPE-PEG2000 lipids to DC8, 9PC in the examined range from 1 mol% to 50 mol % showed a decrease in the transition temperature and altered the associated enthalpy of transition of DC8,9PC bilayer. In week four (Fig. 2b), LNPs with DPSE-PEG 2 K (5) or at 5 mol% demonstrated a significant decrease of 66% in enthalpy with broadened Tm peak and a transition shift to 42.96 ± 0.69 °C from 45 °C. Similarly, 2 K (10) or 10 mol% exhibited a 61% decrease in enthalpy with negligible change in Tm. This decrease in enthalpy after four weeks is attributed to the entanglement of the PEG head groups which leads to steric exclusion and subsequent dehydration of the lipid bilayer. This results in possible disruption of bilayer surface observed as broadened melting peak [88, 89].

The change in enthalpy is also attributed to lateral separation of constituent DC8, 9PC bilayer lipids induced by the presence of DSPE-PEG lipids. Lateral separation, a characteristic of heterogeneity of lipids bilayer [90, 91], was predominant due to the presence of zwitterionic PC and PE and polymeric PEG chain. The intermolecular acyl tails of these lipids as well as the presence of dienes in the tail chain further the heterogeneity of the LNP carriers. Since the DSC studies were performed under constant pressure (P) and volume (V) condition, and according to the first law of thermodynamics,

$$\Delta H_{{({\text{Enthalpy}})}} = \, \Delta U_{{({\text{kinetic}} + {\text{potential energy}})}} + \, \Delta \left( {PV} \right)$$
(2)

The calculated enthalpy is the internal energy or the sum of translational, vibrational, and rotational kinetic energies; and the potential energy arising from intermolecular and intramolecular interactions against the van der Waals forces of hydrocarbon chains in the DC8,9PC, DSPE and PEG molecules similar to the ones reported in our previous work [1, 43, 92]. The fluidity of lipids is affected by temperature specifically, in their melting temperature region which results in change in their van der Waals force and thus impacting the overall enthalpy of the system. It is implied that various constituent lipids of the reported LNPs result undergo molecular interactions and perturbations causing lateral phase separation which is indicated by the broadening of the transition peaks. Since the pressure and volume were constant, Δ(PV) = 0.

The pronounced shift of the melting peak of DC 8, 9 PC toward lower temperature with increasing mole fraction of DSPE-PEG is attributed to several reasons as follows: The presence of intercalated PEG in their amorphous state potentially disrupts the hydrogen bonding between the adjacent PC head groups, thereby destroying the structural arrangement of the head groups. Since the melting transition temperature is affected by the orientation of the head groups, the melting point is decreased as the concentration of DSPE-PEG increases[93, 94]. The presence of salt ions in the HBS buffer presumably induces an osmotic stress \(\left( {\Delta G_{{{\text{os}}}} } \right)\) in the lipid bilayer. The osmotic stress affects the curvature of the bilayer resulting in dramatic decrease of average diameters of the LNPs as observed in Fig. 1 [95].

The shift in temperature associated with gel to crystalline phase \(\Delta T_\text{t}^{{{\text{hyd}}}}\) is given by

$$\Delta T_{{\text{t}}}^{{{\text{hyd}}}} = \Delta T_{{{\text{t}}\infty }}^{{{\text{hyd}}}} \tanh \left( {\frac{{\eta_{{\text{w}}} V_{{\text{w}}} }}{{\xi S_{{\text{L}}} }}} \right)$$
(3)

where \(\eta_{{\text{w}}} V_{{\text{w}}}\) is the number of bound water molecules to the lipid bilayer, \(V_{{\text{w}}}\) the volume of one water molecule, ξ the correlation length of water polarization.

It is been reported that some lipid molecules adopt a Pβ’ ripple phase from the crystalline Lβ phase in order to maintain the shape of the bilayer and to balance the water content in the bilayer. The resultant mixture of rippled tails and liquid disordered phase further reduce the phase transition temperature. The rippled phase has a lower degree of fluidity and resembles the gel phase which occurs at lower temperatures [96, 97].

Upon reduction of molecular weight of PEG from 2000 to 1000 in LNPs formulation at sample concentration of 10 mol %, DSC studies in Fig. 2a indicated no change in the melting temperature; however, the enthalpy showed a decrease by 45% enlisted in Table 2. This increment in enthalpy is the consequence of van der Waals forces. The van der Waals forces between the shorter PEG chains of lipids heads weaken with time resulting in an disrupted bilayer[2].

Effect of higher molecular weight DSPE-PEG (5000) on Phase Transitions of DC 8,9 PC/PEG- DSPE LNPs without HPPH

Contrasting effects of high molecular weight PEG associated with DSPE lipid in DC8,9PC matrix invested at 1, 10 and 20 mol% ratios of PEG5000 using DSC is presented in Fig. 3. As seen from DSC curves, LNPs with higher concentrations > 20 mol% resulted in the disappearance of the melting peak due to lateral phase separation which is also supported by previous report [47].

Fig. 3
figure 3

DSC curves of binary mixtures of DC8, 9PC/DSPE-PEG 5000 LNP’s varying in PEG concentrations

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In the presence of 1 mol% of DSPE-PEG5000 lipids, the Tm was found to be 42.06 ± 0.34 °C at the end of week 1, which increased to 44.11 ± 0.78 °C and accompanied by a 23% decrease in enthalpy shown as narrowing of the melting peak.

At 10 mol% PEG-5000, a slight shift in Tm to 42.92 °C is accompanied by a significant reduction enthalpy by 79%. Slight increase in transition temperature with a significant decrease in enthalpy at the end of four weeks in samples containing DSPE-PEG5000 is attributed to the increased mobility of PEG-5000 by virtue of the increased chain length that results in ancillary inter and intra molecular interactions, increasing the internal energy within the bilayer regions of LNPs. However, at 20 mol%, a very broad peak at 43.17 ± 0.18 °C with an enthalpy of 0.49 ± 0.12 J.g−1, at the end of week 1 was observed. Subsequently, at week 4, there was a shift of Tm to 42.79 ± 0.42 °C, with an increase in 28% enthalpy. The longer the PEG chain length in LNP bilayer, larger are the van der Waals forces the between the PEG molecules in the lipid head group and outer leaflet regions, that furthers higher transition temperatures[98, 99]. The overall reduction in enthalpy in the DSPE-PEG5000 formulations is congruent with formulations containing 10 and 20 mol% DSPE-PEG2000.

Consequently, differential scanning calorimetry studies and thermodynamic correlations provide indications of thermal stability of the LNPs, and resultant molecular perturbations caused integration of DSPE-PEG lipids into the DC8,9 lipid matrix. Additionally, the size analysis supports the physical or steric stability by demonstrating the homogenous nature of the LNP formulations. Based on the DSC and DLS studies, LNPs comprising of 10 mol% DSPE-PEG—1000, 2000 and 5000 lipids, and 20 mol% DSPE-PEG2000 were chosen for encapsulation of HPPH.

Effect of incorporation of HPPH on the DC8, 9PC/DSPE-PEG LNPs

The HPPH-encapsulated LNPs demonstrated monodispersity evidenced by a measured of PDI ≤ 0.2 similar to their unencapsulated LNPs equivalents. However, the presence of HPPH altered the bilayer packing resulting in reduction of LNPs diameter between 5–15% corresponding to the ratio and molecular weight of DSPE-PEG. This variation in LNP diameter is a characteristic lipid packing modification due to the presence of HPPH, which further alters the fluidity of the lipid bilayer that is emulated on DSC curves in Fig. 4.

Fig. 4
figure 4

DSC curves of DC8,9PC/DSPE-PEG formulation in the absence and presence of encapsulated HPPH

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Figure 4 represents the stability of formulations containing 10 and 20 mol% of DSPE-PEG LNPs of varying PEG chain lengths1000, 2000, 5000 in the presence and absence of HPPH in week 1 and week 4, respectively. When compared to unencapsulated LNPs 2 K (10), during week 1, on incorporating HPPH, there is no significant change in the enthalpy of transition and the Tm is shifted to a slightly lower temperature (Tm = 42.06 ± 0.10 °C). In the week 4, 2 K (10)/HPPH, had further shifter to a lower Tm of 41.67 ± 0.48 °C with an enthalpy of transition of 2.05 ± 0.76 J.g−1, which was 40% decrease in enthalpy as compared to the plain sample in Fig. 4b.

Similar trends of lower Tm and enthalpy have been observed in formulations with HPPH has been observed with 1 K (10), 2 K (20) and 5 K (10) as tabulated in Table 3.

Table 3 Comparison of melting temperature and enthalpies of LNP with and without encapsulated HPPH from week 1 to week 4
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It is observed that all the investigated LNPs encapsulating HPPH demonstrated lower enthalpies compared to their unencapsulated equivalents except the LNPs constituting 10 mol% PEG-5000. HPPH being hydrophobic accumulates in the tail region of the bilayer. Structurally, the donor hydrogen electrons in the porphyrin ring of HPPH has donor interacts with the acceptor oxygen electrons in the glycerol moieties of the lipids and form hydrogen bonds[82, 83]. The presence of HPPH in the hydrophobic alkyl tails gives rise to previously discussed van der Waals forces that enables increased tightness of lipid packing and modification of the overall membrane curvature. The formation of these bonds limits the fluidity of the lipid molecules, thereby reducing the internal energy of the lipid bilayer in the presence of HPPH molecules. This change in internal energy is quantified by computing the enthalpy of transition summarized in Table 3.

The significant increase in enthalpy of LNPs consisting of 10 mol% of PEG-5000 is assumed due to the strong van der Waals force arising from the intercalation of longer DSPE-5000 PEG chains, which counteracts the presence of HPPH. This results in an increased curvature of the LNP rendering them unsuitable for drug delivery applications.

It is inferred from the size and DSC studies that out of four of the formulations that encapsulated HPPH, 2 K (10)/HPPH is the optimum formulation because size of the carrier (104 nm) is well within the standard size range of the nano-carriers (70–200 nm) used in drug delivery.

The reduction of enthalpy in the presence of HPPH, which corresponds to phase separation of formulation, at the end of week 4 is not significant compared to 2 K (10) in Week 4. This is presumed due to the optimum van der Waals force that counteracts the presence of HPPH in the hydrophobic tail region and is responsible for the stability of the formulation as shown in Fig. 5. This work facilitates the significance of thermal stability studies in development of lipid-based carriers and vaccines [100,101,102] which are susceptible to temperatures[103,104,105,106,107]. This model study can potentially be applied to design thermally stable lipid-based vaccines including the anticipated COVID-19 vaccine for their prolonged stability during their storage, transportation, and distribution.

Fig. 5
figure 5

Schematic representation of bond formations between HPPH with various moieties on lipid headgroup and tails

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Conclusions

In this work, we demonstrate the thermal and steric stability of HPPH-encapsulated lipid-based carriers imparted by PEGylated lipids. A systematic investigation was conducted using DSC on the effects of varying molecular mass and concentrations of PEG polymers in the photopolymerizable lipid DC8, 9PC lipid bilayer matrix. Intuitively, the lower concentration of PEG-lipids demonstrated higher stability to reduced phase separation arising from heterogeneity in the lipid bilayer. It was found that both smaller and larger PEG chains- 1 K and 5 K thermally unstable formulations; however, PEG-2 K resulted in stable formulations due to their optimum size that results in van der Waal interactions with lipid groups. It was observed that the encapsulation of HPPH enhanced the thermal stability via formation of hydrogen bonds with lipid moieties that increased the packing order of the bilayer comprising of PEG-2 K molecules. These formulations have previously showed efficacy in vivo studies. It is concluded that the encapsulation of therapeutics in lipid formulations can alter their overall thermal stability. It is postulated that the research methodologies and findings presented in this work can also be applied to predict the stability of lipid-based vaccines during their storage, transport, and distribution.