Novel preparation method for sustained-release PLGA microspheres using water-in-oil-in-hydrophilic-oil-in-water emulsion.

An increasing number of drugs are needing improved formulations to optimize patient compliance because of their short half-lives in blood. Sustained-release formulations of drugs are often required for long-term efficacy, and microspheres are among the most popular ones. When drugs are encapsulated into microsphere formulations, different methods of preparation need to be used according to specific clinical requirements and the differing physicochemical characteristics of individual drugs. In this work, we developed a novel method for sustained-release drug delivery using a water-in-oil-in-hydrophilic oil-in-water (w/o/oh/w) emulsion to encapsulate a drug into poly(lactic-co-glycolic acid) (PLGA) microspheres. Different effects were achieved by varying the proportions and concentrations of hydrophilic oil and PLGA. Scanning electron and optical microscopic images showed the surfaces of the microspheres to be smooth and that their morphology was spherical. Microspheres prepared using the w/o/oh/w emulsion were able to load protein efficiently and had sustained-release properties. These results indicate that the above-mentioned method might be useful for developing sustained-release microsphere formulations in the future.

Introduction

The physicochemical characteristics of different drugs vary considerably, so different microsphere formulations are often developed according to specific clinical need. Emulsion methods are most commonly used to prepare microspheres, eg, water-in-oil (w/o),1 water-in-oil-in-water (w/o/w),2,3 water-in-oil-in-oil (w/o/o),4 oil-in-water (o/w),5 solid-in-oil-in-water (s/o/w),6–13 and solid-in-oil-in-oil (s/o/o).14,15 A w/o/w process is applied when a solvent evaporation technique is used to encapsulate protein or peptide drugs, whereby the active protein first needs to be dissolved in aqueous inner phase. However, use of protein or peptide drugs in aqueous solution results in the presence of a water/organic interface that might compromise the stability of the encapsulated protein or peptide drug. Further, permeation of emulsion droplets from inner water phase into outer water phase results in relatively low encapsulation efficiency (EE). To solve these problems, s/o/w or s/o/o methods have been used to encapsulate protein or peptide drugs, in which the drug powder is directly dispersed in organic phase, with subsequent addition of the suspension to outer water phase.21–27 Whichever s/o/o or s/o/w technique is used, it is essential to use a pretreatment to reduce the particle size of the protein or peptide drug in the powder to 1–10 μm before the first s/o suspension step. Lyophilization of a water solution containing a protein or peptide drug with additives is widely performed. However, denaturing and aggregation of protein and peptide drugs is common during freezing and subsequent dehydration, even in the presence of lyoprotectors. Further, traditional s/o/w emulsions are generally emulsified using intense mechanical force generated by a homogenizer, which can damage the bioactivity of a protein or peptide drug.21–27 Also, such methods cannot address the problems in achieving sustained-release properties for all drugs, because different drugs have different physicochemical characteristics.

We have developed s/o/o/w and s/o/o/ethanol (e) emulsions for preparation of protein microspheres.16,17 However, a method for preparation of poly(lactic-co-glycolic acid) (PLGA) microspheres using a water-in-oil-in-hydrophilic oil-in-water (w/o/oh/w) emulsion to achieve sustained-release drug delivery has not been developed as yet. Therefore, in this study, we developed a novel method for preparation of an emulsion to carry spherical-shaped drug-loaded microspheres for sustained drug release.

Materials and methods

Materials

PLGA 3A dl (lactide to glycolide ratio 50:50, molecular weight 47,000), 2A dl (lactide to glycolide ratio 50:50, molecular weight 13,000), and polylactide (LPLA, molecular weight 60,000, low viscosity; HPLA, molecular weight 83,000, high viscosity) were obtained from Lakeshore Biopolymers Inc (Cincinnati, OH, USA). Poly(vinyl alcohol) (PVA, molecular weight 30,000–50,000, 87%–89% hydrolyzed) was purchased from Sigma (St Louis, MO, USA). Phosphate-buffered solution (pH 7.2) and a micro bicinchoninic acid protein assay kit were sourced from Pierce (Rockford, IL, USA). Dichloromethane, polyethylene glycol (molecular weight 8000), ethylene glycol, 1,2-propylene glycol, glycerol, polyvinyl-pyrrolidone, poloxamer 188, and trehalose were obtained from the Sinopharm Chemical Reagent Co., Ltd (Shanghai, People’s Republic of China). Bovine serum albumin was sourced from Siji Company (Shanghai, People’s Republic of China). All chemicals were used without further purification.

Preparation of protein-loaded microspheres using the w/o/oh/w method

First, 1 mL of drug or water was dispersed in 5 mL of different concentrations of PLGA, PLA, and dichloromethane solutions by stirring at a rotation speed of 2500 rpm for one minute using a homogenizer (FA25, Fluko, Shanghai, People’s Republic of China). The mixture was then dispersed into hydrophilic oil phase (ethylene glycol to glycerol ratio 4:1; 1,2-propylene glycol to glycerol ratio 4:1) containing 1% w/w PVA and 5% w/w NaCl water solution with agitation using an electromotive stirrer (JJ-1, Jintan Xinhang Co, Ltd, Jiangsu, People’s Republic of China) equipped with two-plate shaft stirring at 1200 rpm and 4°C for five minutes. Hydrophilic oil phase was used to extract the organic solvent from the oil phase and also to dissolve the aqueous phase and enhance solidification of the PLGA microspheres. The mixed emulsion was solidified in 5% NaCl water solution with stirring continued at 200 rpm for four hours to extract the organic solvent. The solid microspheres were collected by centrifugation (Anker TGL-16C, Ningbo Tianyu Optoelectronic Technology, Ningbo, People’s Republic of China) at 2000 rpm, then washed three times with distilled water and freeze-dried using a lyophilizer (Christ Alpha 1–2, Martin Christ Gefriertrocknungsanlagen GmbH, Osterode am Harz, Germany) at 40°C for 24 hours.

Scanning electron and optical microscopy

A scanning electron microscope (SEM, Sirion, Hillsboro, OR, USA) was used to obtain electron microscopic images of the microspheres, and an optical microscope (CX-41, Olympus, Tokyo, Japan) was used to obtain optical images. The microspheres were attached to double-edged conductive tape attached to the SEM specimen holders. The microspheres were then coated with a layer of gold by spraying of gold vapor for 10 minutes under an argon atmosphere, with images recorded at a sputtering energy of 5 kV under high vacuum.

Size distribution of microspheres

The mean particle size and size distribution of the microspheres were measured using a particle size and shape analyzer (CIS-100, Ankersmid, Nijverda, The Netherlands) with a laser wavelength of 633 nm. The microspheres to be measured were suspended in the quartz sample holder filled with isopropyl alcohol and subjected to magnetic stirring.

Size exclusion high-performance liquid chromatography

A size exclusion high-performance liquid chromatography (SEC-HPLC) assay was carried out using an HPLC system equipped with a TSK G2000Sk-XL1 column (Younglin, Kyounggi-do, Republic of Korea). The mobile phase comprised 0.15 M sodium chloride and 50 mM sodium phosphate (pH 7.25), and chromatographic charts were recorded at an ultraviolet detection wavelength of 214 nm. Next, 100 μL of each sample of dissolved protein was filtered using a 0.22 μm filter (Millipore, Billerica, MA, USA) and injected into the HPLC system at a mobile phase flow rate of 1.0 mL per minute. The amounts of native protein monomers and aggregates present were calculated from the monomer and aggregate peaks, respectively. The results are expressed as peak percentages of the total area.

Micro bicinchoninic acid and β-galactosidase activity assays

The concentration of the protein samples was determined using a micro bicinchoninic acid protein kit. To examine how the bioactivity of proteins could be preserved during the PLGA microsphere preparation process, β-galactosidase, a protein with a quaternary structure and molecular weight of over 500 kDa, was loaded into the system and recovered at each step for assay of activity. Trehalose 1% (w/w) as the mass of dextran was added to the solution for lyoprotection. The bioactivity of the recovered protein was assayed by hydrolysis of o-nitrophenyl-b-D-galactopyranoside (the substrate), which generated a colored product absorbing photons at 410 nm.

In vitro release test

The in vitro release kinetics of the microspheres were investigated in phosphate-buffered solution (pH 7.2) at 37°C. First, 25 mg of microspheres was suspended in a 5 mL test tube containing 2 mL of phosphate-buffered solution. The sample tubes were then placed in an incubator (KYC 100C, Shanghai Fuma Laboratory Equipment, Shanghai, People’s Republic of China) and shaken horizontally at 110 rpm. At a preset time following incubation, the microspheres were retrieved from the solution by centrifugation at 1000 rpm and 4°C. The supernatant release medium was withdrawn and replaced with fresh phosphate-buffered solution each day, with determination of the protein concentration using a micro bicinchoninic acid assay kit.7–13,16–18

Results and discussion

Characterization of composite microspheres

Figures 1 and 2 show optical microscopic images of the composite microspheres. Figure 1 shows the free solidified microspheres and Figure 2 shows hardened freeze-dried microspheres which differed in their transmittance. Figure 3 is an SEM image of the microspheres, showing smooth surfaces and small holes, possibly because the organic solvent was extracted rapidly from the inner layers of the PLGA microspheres. Figure 4 is an optical microscopic image of the microparticles and Figure 5 is an SEM image of the recovered microspheres, showing that encapsulation of bovine serum albumin and dextran water solution into the microspheres formed freely aggregated microparticles 1–5 μm in size. This was possibly because bovine serum albumin and dextran led to freezing-induced phase separation and self-formed microparticles during freeze-drying.18–20 These microspheres were spherical in shape with diameters in the range of 20–100 μm (Figure 6).

Figure 1

Optical microscopic images of free solidified microspheres. (A) PLGA (3A50/50), (B) PLGA (3A50/50)/LPLA = 40/80, (C) PLGA (3A50/50)/HPLA = 40/60, (D) PLGA (3A50/50)/HPLA = 40/80, (E) PLGA (2A50/50)/HPLA = 40/80, and (F) PLGA (2A50/50)/LPLA = 40/80. W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water cosolution; Oh, PG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent. (G) PLGA (3A50/50)/LPLA = 40/80 and (H) PLGA (3A50/50)/HPLA = 40/80. W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%

Figure 2

Optical microscopic images of solidified microspheres. W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase, 10% of 1200 mg dichloromethane solvent. (A) PLGA (3A50/50), (B) PLGA (3A50/50)/LPLA = 40/80, (C) PLGA (3A50/50)/HPLA = 40/60, (D) PLGA (3A50/50)/HPLA = 40/80; (E) PLGA (2A50/50)/HPLA = 40/80, and (F) PLGA (2A50/50)/LPLA = 40/80. W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water cosolution; Oh, PG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent. (G) PLGA (3A50/50)/LPLA = 40/80 and (H) PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%.

Figure 3

Scanning electron micrographs of microspheres prepared using PLGA (3A50/50) (A), and PLGA (3A50/50)/HPLA (B). W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, PLGA (3A50/50)/HPLA = 40/80, 1200 mg of dichloromethane solvent.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol).

Figure 4

Optical microscopic images of protein dextran microparticles recovered from microspheres. (A) W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, PLGA (3A50/50)/LPLA = 40/80; 1200 mg of dichloromethane solvent; (B) W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, PG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase, 10% PLGA (3A50/50)/LPLA = 40/80, 1200 mg of dichloromethane solvent.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%.

Figure 5

Scanning electron micrographs of protein dextran recovered from microspheres. (A) W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%; PLGA (3A50/50)/LPLA = 40/80, 1200 mg of dichloromethane solvent. (B) W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, PG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL, oil phase 10%; PLGA (3A50/50)/LPLA = 40/80, 1200 mg of dichloromethane solvent.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); PVA, poly(vinyl alcohol); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%.

Figure 6

Distribution of microspheres. W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, PG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL, oil phase 10%; PLGA (3A50/50)/LPLA = 40/80, 1200 mg of dichloromethane solvent.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); PVA, poly(vinyl alcohol); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; dV/dD, d volume/d density; SD, standard deviation.

Encapsulation efficiency

Effect of viscosity of materials

Table 1 shows a significant discrepancy in EE between LPLA and HPLA formed using the w/o/oh/w method. The EE of composite LPLA microspheres was significantly higher than that of the HPLA microspheres. This is possibly because the HPLA was more hydrophobic than the LPLA, and bovine serum albumin was hydrophilic whereas protein and dextran were also hydrophilic and more easily adsorbed onto the hydrophilic LPLA.

Table 1

Effect of PLGA/PLA ratio on loading efficiency and encapsulation efficiency (n = 3)

Formulation	Loading efficiency (% ± SD)	Encapsulation efficiency (% ± SD)
(A) PLGA3A	1.41 ± 0.09	31.04 ± 1.98
(B) PLGA3A:LPLA	1.39 ± 0.19	30.58 ± 4.18
(C) PLGA3A:HPLA	0.96 ± 0.09	19.58 ± 1.98

Notes: W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent. (A) PLGA (3A50/50), (B) PLGA (3A50/50)/LPLA 40/80, and (C) PLGA (3A50/50)/HPLA 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; PVA, poly(vinyl alcohol); PLA, polylactide; SD, standard deviation.

Effect of hydrophobic properties of materials

Table 2 shows a significant discrepancy in EE between PLGA 2A and PLGA 3A when the w/o/oh/w method was used. The EE of the composite PLGA 2A microspheres was significantly higher than that of the PLGA 3A microspheres. This is possibly because PLGA 3A was more hydrophobic than PLGA 2A, while bovine serum albumin was hydrophilic.

Table 2

Effect of PLGA to PLA ratio on loading and encapsulation efficiency (n = 3)

Formulation	Loading efficiency (% ± SD)	Encapsulation efficiency (% ± SD)
(I) PLGA2A:HPLA = 40:80	1.68 ± 0.11	39.96 ± 2.18
(II) PLGA2A:LPLA = 40:80	2.01 ± 0.13	44.22 ± 2.84
(III) PLGA3A:LPLA = 40:80	1.39 ± 0.19	30.58 ± 4.18
(IV) PLGA3A:HPLA = 40:80	0.96 ± 0.09	19.58 ± 1.98

Notes: W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent. Formulation (I), PLGA (2A50/50)/LPLA = 40/80; formulation (II), PLGA (2A50/50)/HPLA = 40/80; formulation (III) PLGA (3A50/50)/LPLA = 40/80; formulation (IV), PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; PVA, poly(vinyl alcohol); PLA, polylactide; SD, standard deviation.

Effect of ratio of PLGA 3A to HPLA

Table 3 shows a significant discrepancy in EE according to the PLGA 3A and HPLA ratio when the w/o/oh/w method was used. The EE of the high ratio PLGA 3A and HPLA microspheres was significantly higher than that of low ratio PLGA 3A microspheres. This may be because the high ratio PLGA 3A materials were more hydrophilic than the low ratio PLGA 3A materials, while bovine serum albumin was hydrophilic.

Table 3

Effect of PLGA to PLA ratio on loading and encapsulation efficiency (n = 3)

Formulation	Loading efficiency (% ± SD)	Encapsulation efficiency (% ± SD)
(I) PLGA3A:HPLA = 40:60	1.17 ± 0.22	25.74 ± 4.84
(II) PLGA3A:HPLA = 40:80	0.96 ± 0.09	19.58 ± 1.98

Notes: W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent; formulation (I) PLGA (3A50/50)/HPLA = 40/60; formulation (II) PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; PLA, polylactide; SD, standard deviation.

Effect of hydrophilic oil phase

Table 4 shows a significant discrepancy in EE between the hydrophilic oil phase of the ethylene glycol and glycerol mixture and the hydrophilic oil phase of the 1,2-propylene glycol and glycerol mixture using the w/o/oh/w method. The EE of the composite microspheres was significantly higher when using the hydrophilic oil phase of the ethylene glycol and glycerol microspheres. This could be because ethylene glycol was more hydrophilic than 1,2-propylene glycol, while bovine serum albumin was hydrophilic.

Table 4

Effect of different Oh on loading efficiency and encapsulation efficiency (n = 3)

Formulation	Loading efficiency (% ± SD)	Encapsulation efficiency (% ± SD)
A	0.83 ± 0.12	18.26 ± 2.64
B	1.32 ± 0.22	29.04 ± 4.84
C	0.96 ± 0.09	21.12 ± 1.98
D	1.39 ± 0.19	30.58 ± 4.18

Notes: W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, PG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent. Formulation A, PLGA (3A50/50)/LPLA = 40/80; formulation B, PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; SD, standard deviation.

Integrity of proteins at each formulation step

In this study, protein aggregation after each microencapsulation step was assayed for myoglobin and bovine serum albumin using SEC-HPLC. The results are shown in Table 5. The amounts of aggregated myoglobin and bovine serum albumin were observed before and after each of the formulation steps. There was no significant decrease in the amount of protein monomer observed after each formulation step (lyophilization followed by washing with dichloromethane and microencapsulation into PLGA microspheres followed by recovery).

Table 5

Amount of myoglobin and BSA protein aggregated before and after each formulation step (n = 5)

	Aggregated protein (% ± SD)
Original BSA	12.12 ± 1.12
Original myoglobin	10.09 ± 1.59
BSA from microspheres	11.90 ± 2.02
Myoglobin from microspheres	10.39 ± 0.99

Abbreviations: BSA, bovine serum albumin; SD, standard deviation.

Protein activity during formulation steps

With regard to protein activity during the formulation steps, the EE of β-galactosidase was 85.1% ± 1.2% by the w/o/oh/w method and 60.2% ± 4.3% by w/o/w. Figure 7 compares the activity recovery rate between proteins from microspheres prepared using the conventional w/o/w method and those prepared using the novel w/o/oh/w method. For protein protected using the abovementioned novel method of microencapsulation, more than 78% (w/w) of β-galactosidase activity was preserved, while for protein protected using the w/o/w method, the recovery rate was 40% (w/w).

Figure 7

Comparison of recovery rates for protein activity from microspheres prepared using the different methods (n = 3).

Abbreviation: β-gal, β-galactosidase; w/o/w, water-in-oil-in-water.

In vitro release study

Effect of material viscosity

Figure 8 shows that the burst release decreased and incomplete release increased in the order of PLGA, LPLA, and HPLA. This may be because the rate of material degradation decreased in the same order of PLGA, LPLA, and HPLA.

Figure 8

Effect of ratio of PLGA/PLA on release in vitro (n = 3). W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL, oil phase 10%, 1200 mg of dichloromethane solvent. (A) PLGA (3A50/50), (B) PLGA (3A50/50)/LPLA = 40/80, and (C) PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; PLA, polylactide.

Figure 9 shows that the burst release decreased and incomplete release increased in the order of PLGA 2A, PLGA 3A, LPLA, and HPLA. This may be because the rate of material degradation decreased in this order.

Figure 9

Effect of different materials on release in vitro. W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent; formulation I, PLGA (2A50/50)/LPLA = 40/80; formulation II, PLGA (2A50/50)/HPLA = 40/80; formulation III, PLGA (3A50/50)/LPLA = 40/80; formulation IV, PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); LPLA, low viscosity polylactide (molecular weight 60,000); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%.

Effect of PLGA 3A and HPLA ratio

Figure 10 shows that the burst release decreased and incomplete release increased in the order of high ratio PLGA 3A then low ratio PLGA 3A. This was possibly because the rate of material degradation decreased in the same order.

Figure 10

Effect of PLGA/PLA ratio on release in vitro. W1, 5% w/w BSA and dextran (BSA to dextran 6 mg:6 mg) water solution; Oh, DEG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent; formulation I, PLGA (3A50/50)/HPLA = 40/60; formulation II, PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); Oh, hydrophilic oil; DEG/G, ethylene glycol/glycerol; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; PLA, polylactide.

Figure 11 shows that the burst release decreased and incomplete release increased in the order of ethylene glycol then 1,2-propylene glycol because of their different hydrophilic properties.

Figure 11

Effect of different Oh on release in vitro (n = 3). W1, 5% w/w BSA and dextran (BSA to dextran ratio 6 mg:6 mg) water solution; Oh, PG/G = 4 (5.5 mL containing 0.5 mL of 1% PVA and 5% NaCl); W2, 5% NaCl 1000 mL; oil phase 10%, 1200 mg of dichloromethane solvent; formulation A, PLGA (3A50/50)/LPLA = 40/80; formulation B, PLGA (3A50/50)/HPLA = 40/80.

Abbreviations: BSA, bovine serum albumin; PLGA, poly(lactic-co-glycolic acid); HPLA, high viscosity polylactide (molecular weight 83,000); PVA, poly(vinyl alcohol); PG/G, 1, 2-propylene glycol/glycerol; Oh, hydrophilic oil; NaCl, sodium chloride; W1, 1% PVA and 5% NaCl water solution; W2, 5% NaCl water solution; w/w, trehalose 1%; LPLA, low viscosity polylactide (molecular weight 60,000).

Conclusion

In this study, we developed a novel method for preparation of sustained-release drug-encapsulating microspheres using a w/o/oh/w emulsion. We selected a hydrophilic oil phase to replace the second water phase (containing PVA and NaCl) used in our previous research to extend the formulation method s/o/o/e. Use of hydrophilic oil was helpful for avoiding dissolution of particles and thereby increasing the protein EE. This also helped to avoid the dissolved protein from coming into contact with the oil-water surface, which could denature the proteins. We investigated many factors which might affect the morphology, size distribution, EE, and release profiles of the microspheres, and found that the hydrophilic and hydrophobic properties of the different materials used and the hydrophilic oil phase were key factors. Composite microspheres, with spherical morphology, suitable particle size, and good drug stability during the formulation steps and in vitro release, were successfully formulated.

This research has helped to resolve the technical issues involved in preparation of sustained-release microspheres for encapsulating drugs. PLGA is a biocompatible material, and has been used in clinical applications for many years. When PLGA microspheres are 20–100 μm in size, they usually inhibit uptake of cells and depend only on degradation and uptake of PLGA.

This novel method may enhance the bioactivity and EE of proteins because of the decreased interface between oil and water. The materials are often modified to be more hydrophilic in order to enhance the bioactivity and EE of proteins. We have developed a new method to address this problem by adding a hydrophilic oil phase and decreasing the amount of protein directly in contact with the interface between oil and water.