Patent Application
20140356442
The present invention relates to the field of pharmaceutical preparations and, particularly, to a composition of long-acting sustained release triptorelin microspheres, methods for preparing the same and use of the same.
Gonadotropin-releasing hormone (GnRH), also known as luteinizing hormone-releasing hormone (LHRH), is a decapeptide hormone closely related to reproductive functions. When an exogenous LHRH or an analogue thereof is administrated with a physiological pulse frequency (once per 90 min) for a short period and at a small dose, it produces some promoting effects to the pituitary-gonadal system, and hence is used clinically for treating symptoms such as sexual dysfunction, anovulation, delayed puberty, etc. When it is administrated with a non-physiological pulse frequency for a long period and at a large dose, it can inhibit the hypophysis from secreting luteinizing hormone and follicle stimulating hormone, resulting in a decrease in the hormone secretion capacity of gonad and the atrophy of sexual organs. It is thus used clinically for treating some hormone-dependent diseases such as prostate cancer, hysteromyoma, breast carcinoma, adenomyosis, precocious puberty, etc. The LHRH and analogues thereof used clinically at the moment include triptorelin, buserelin, gonadorelin, leuprorelin, goserelin, etc.
Triptorelin is a synthetic LHRH analogue. Triptorelin modifies the structure of LHRH by substituting the sixth glycine in the natural LHRH with a D-tryptophan. Its bioactivity is 100 times of the natural LHRH, and it has significant effects in treating diseases such as prostate cancer, adenomyosis, hysteromyoma, breast carcinoma, etc.
The administration of triptorelin to its clinical indications typically requires a patient be on the medication for a long period. Thus, in order to improve patient compliance, triptorelin has been developed into long-acting sustained release preparations. Currently, the commercially available long-acting sustained release preparations of triptorelin are microsphere injections, including the products for administration once per 4 weeks, once per 12 weeks, and once per 24 weeks.
It is recognized that triptorelin must be administrated at large doses for a long period of time in order to decrease the gonadal hormone secretion capacity of the gonad and the atrophy of sexual organs, thus achieving the purpose of treating diseases such as hormone-dependent prostate cancer, etc. (Qinghua Chen et al., Development in research on microsphere drug delivery systems of polypeptide and protein drugs, Foreign Medical Sciences—Section on Pharmacy, 1997, 24(3): 129-133). Accordingly, unlike most other pharmaceutical microspheres, for which the smaller the initial release the better, an ideal long-acting microsphere preparation of triptorelin, after its injection, needs a relatively large initial release, so as to maintain the pharmaceutical effects until a later stage of drug delivery. Several LHRH analogue microspheres, which have been commercially available, are mostly of this drug release mode, for example, the microspheres of leuprorelin have an initial release up to above 20% in 1-2 days (Qinghua Chen et al., Development of research on microsphere drug delivery systems of polypeptide and protein drugs, Foreign Medical Sciences—Section on Pharmacy, 1997, 24(3): 129-133), while the triptorelin pamoate microspheres from Debiopharm S.A. have a drug release of up to above 40% in 1-2 days, during that time the concentration of testosterone in blood plasma rises in the early stage of drug delivery, reaches a maximum value on about the 4th day, and then decreases to a castration level, thus producing the pharmaceutical effects thereof (American FDA documents, FDA Application No: (NDA)020715).
However, the triptorelin microspheres prepared by a double emulsion-solvent evaporation process have a very low initial release, which makes the drug incapable of acting as soon as possible after its administration. Thus, there remains a need for developing extended release triptorelin microspheres that achieve a high initial release profile.
Described herein are embodiments directed to triptorelin microspheres incorporating glucose or mannitol. As a result, the initial release of the drug in vivo can be increased, thus promoting the drug to act as soon as possible. The present disclosure thus provides a pharmaceutical composition of sustained release triptorelin microspheres, the triptorelin microspheres comprising triptorelin or a salt thereof, copolymers of lactide and glycolide, and glucose or mannitol, wherein the content by weight of glucose or mannitol is 0.1-10%, or 0.5-10%, or 0.5-5%, or 0.5-2%, or 1%; the content by weight of triptorelin or the salt thereof is 1-30%, or 2-20%, or 5-15%; the content by weight of copolymers of lactide and glycolide is 60-98.9%, or 75-97.8%, or 83-94.5%.
Specifically, in the pharmaceutical composition of sustained release triptorelin microspheres of the present invention, the content by weight of triptorelin or the salt thereof is 1-30%, the content by weight of copolymers of lactide and glycolide is 60-98.9%, the content by weight of glucose or mannitol is 0.1-10%.
In the pharmaceutical composition of sustained release triptorelin microspheres of the present invention, the content by weight of triptorelin or the salt thereof is 2-20%, the content by weight of copolymers of lactide and glycolide is 70-97.5%, the content by weight of glucose or mannitol is 0.5-10%.
In the pharmaceutical composition of sustained release triptorelin microspheres of the present invention, the content by weight of triptorelin or the salt thereof is 2-20%, the content by weight of copolymers of lactide and glycolide is 75-97.5%, the content by weight of glucose or mannitol is 0.5-5%.
In the pharmaceutical composition of sustained release triptorelin microspheres of the present invention, the content by weight of triptorelin or the salt thereof is 5-15%, the content by weight of copolymers of lactide and glycolide is 83-94.5%, the content by weight of glucose or mannitol is 0.5-2%.
In the pharmaceutical composition of sustained release triptorelin microspheres of the present invention, the content by weight of triptorelin or the salt thereof is 10%, the content by weight of copolymers of lactide and glycolide is 89%, the content by weight of glucose or mannitol is 1%.
The microspheres as disclosed herein is: Small spherical or spherical-like particles consist of drug dissolved and (or) dispersed homogeneously throughout a polymer material, with a particle size ranging in 1-500 μm, and generally prepared as suspensions for injection.
The copolymers of lactide and glycolide is also referred to as poly(lactide-co-glycolide), abbreviated as PLGA. The molar ratio of lactide to glycolide in said PLGA is 100:0 to 40:60, or 90:10 to 40:60, or 75:25 to 40:60, or 60:40 to 40:60, or 50:50.
The intrinsic viscosity of PLGA is 0.10-0.70 dL/g, preferably in the range of 0.15-0.50 dL/g, and optimally in the range of 0.20-0.35 dL/g. A method for measuring the intrinsic viscosity of PLGA is as follows: preparing an about 0.5% (w/v) solution of PLGA in chloroform, and determining the intrinsic viscosity of PLGA at 30° C. using a Cannon-Fenske glass capillary viscometer.
The PLGA described in the present invention may have a molecular weight of 5,000-100,000 Dalton, preferably 10,000-75,000 Dalton, and more preferably 15,000-40,000 Dalton. As used herein, the term “molecular weight” refers to “weight average molecular weight.”
As used herein, the molar ratio of lactide to glycolide and the intrinsic viscosity of PLGA are shown hereinafter in brackets. For example, “PLGA (75/25, 0.5, 75000)” represents poly(lactide-co-glycolide) with a molar ratio of lactide to glycolide of 75:25, an intrinsic viscosity of 0.5 dl/g and a molecular weight of 75,000 Dalton.
The drug loading amount described in the present invention is the actual drug loading amount, which is calculated as follows: drug loading amount=[amount of drug in microspheres/(amount of drug in microspheres+amount of polymers)]×100%.
The salt of triptorelin in the sustained release microsphere provided by the present invention can be a water-soluble salt such as acetates, etc.
The sustained release triptorelin microspheres provided by the present invention is prepared by a conventional double emulsion-solvent evaporation process, wherein the glucose or mannitol is added into an inner water phase, and a preferred process is as follows: PLGA is dissolved in dichloromethane to form an oil phase, triptorelin and glucose or mannitol are weighted and dissolved in deionized water to form a water phase; the water phase is added into the oil phase, and then subjected to shearing emulsification so as to obtain a w/o primary emulsion. Then, the primary emulsion is added into a polyvinyl alcohol (PVA) solution, homogeneously emulsified to obtain a w/o/w double emulsion, then the organic solvent is removed therefrom, and the residue is washed and filtered to obtain the microspheres.
The present invention further provides a use of the triptorelin microspheres in preparing drugs for treating prostate cancer, sexual precocity, adenomyosis, female infertility, and hysteromyoma.
The microspheres provided by the present invention can be made into the form of sterile powder, wherein the sterile powder comprises the composition of triptorelin microspheres and mannitol, and it can be prepared as follows: rinsing the composition of triptorelin microspheres with water for injection and transferring into a freeze-drying tray, adding mannitol and a proper amount of water for injection therein, placing the freeze-drying tray in a freeze drier for freeze-drying; and subjecting the freeze-dried product to sieving and mixing, aseptic filling and capping, so as to obtain the sterile powder. Before being administrated to a patient, the sterile powder is suspended in a pharmaceutically acceptable dispersion solvent, wherein the dispersion solvent may be one or more of a suspending agent, a pH regulator, an isoosmotic adjusting agent and a surfactant, together with water for injection; the suspending agent may be one or more of sodium carboxymethyl cellulose, polyvinyl alcohol, polyvinylpyrrolidone, sodium alginate, and glycerol; the isoosmotic adjusting agent may be one or more of sodium chloride, glucose, mannitol and sorbitol; and the surfactant is a nonionic surfactant, such as polysorbate series (e.g., polysorbate 80, polysorbate 60, etc.), or triblock copolymers of poly(propylene glycol) flanked by poly(ethylene glycol), sold under the trade name of Poloxamer (e.g., Poloxamer 188, etc.).
The sustained release triptorelin microspheres provided by the present invention is used for intramuscular or subcutaneous injection, with the administration dose thereof being 3.75 mg/28 days (calculated by the amount of
The present disclosure will be further illustrated by the following examples and test examples, which will not limit the scope of the present invention in any way.
1.76 g of PLGA (50/50, 0.51, 75000) was weighed and dissolved in 6 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 40 mg of glucose were weighed and dissolved in 0.6 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 17500 rpm for 60 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 0.5% PVA solution at 6° C. through an injector under homogenizing at 1500 rpm, and then it was homogeneously emulsified for 2 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.42% and an entrapment efficiency of 94.2%.
1.46 g of PLGA (65/35, 0.37, 45000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 400 mg of triptorelin acetate and 140 mg of glucose were weighed and dissolved in 1.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 15000 rpm for 60 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 6° C. through an injector under homogenizing at 1800 rpm, and then it was homogeneously emulsified for 4 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 17.82% and an entrapment efficiency of 89.1%.
1.698 g of PLGA (75/25, 0.50, 70000) was weighed and dissolved in 12 ml of dichloromethane to form an oil phase, 300 mg of triptorelin acetate and 2 mg of glucose were weighed and dissolved in 1.2 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 2.0% PVA solution at 4° C. through an injector under homogenizing at 1500 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 500 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 13.71% and an entrapment efficiency of 91.4%.
1.50 g of PLGA (75/25, 0.50, 70000) was weighed and dissolved in 12 ml of dichloromethane to form an oil phase, 300 mg of triptorelin acetate and 200 mg of glucose were weighed and dissolved in 1.2 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 17500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 4° C. through an injector under homogenizing at 2000 rpm, and then was homogeneously emulsified for 4 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 400 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 13.52% and an entrapment efficiency of 90.13%.
1.88 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 100 mg of triptorelin acetate and 20 mg of glucose were weighed and dissolved in 1.0 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 6° C. through an injector under homogenizing at 2100 rpm, and then was homogeneously emulsified for 2 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 4.59% and an entrapment efficiency of 91.8%.
1.80 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 100 mg of triptorelin acetate and 100 mg of glucose were weighed and dissolved in 1.0 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 6° C. through an injector under homogenizing at 2100 rpm, and then was homogeneously emulsified for 2 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 4.67% and an entrapment efficiency of 93.4%.
1.90 g of PLGA (90/10, 0.42, 53000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 40 mg of triptorelin acetate and 60 mg mannitol were weighed and dissolved in 1.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 180 s to obtain a primary emulsion. The primary emulsion was added into a reaction kettle containing 1000 ml of a 1.0% PVA solution at 10° C. through an injector under homogenizing at 1800 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. With a rotation speed of 600 rpm, it was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 1.84% and an entrapment efficiency of 92.0%.
1.698 g of PLGA (75/25, 0.49, 70000) was weighed and dissolved in 12 ml of dichloromethane to form an oil phase, 300 mg of triptorelin acetate and 2 mg mannitol were weighed and dissolved in 1.2 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 15000 rpm for 180 s to obtain a primary emulsion. The primary emulsion was added into a reaction kettle containing 1000 ml of a 1.0% PVA solution at 10° C. through an injector under homogenizing at 1800 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. With a rotation speed of 600 rpm, it was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 13.84% and an entrapment efficiency of 92.3%.
1.88 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 100 mg of triptorelin acetate and 20 mg mannitol were weighed and dissolved in 1.0 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 6° C. through an injector under homogenizing at 2100 rpm, and then was homogeneously emulsified for 2 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 4.53% and an entrapment efficiency of 90.6%.
1.80 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 100 mg of triptorelin acetate and 100 mg mannitol were weighed and dissolved in 1.0 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 6° C. through an injector under homogenizing at 2100 rpm, and then was homogeneously emulsified for 2 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 4.63% and an entrapment efficiency of 92.6%.
1.86 g of PLGA (100/0, 0.37, 50000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 100 mg triptorelin acetate and 40 mg of glucose were weighed and dissolved in 1.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 120 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 10° C. through an injector under homogenizing at 2000 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 4.74% and an entrapment efficiency of 94.8%.
3.64 g of PLGA (75/25, 0.68, 100000) was weighed and dissolved in 40 ml of dichloromethane to form an oil phase, 40 mg of triptorelin acetate and 320 mg of glucose were weighed and dissolved in 4.0 ml of water to form a water phase; and then the oil phase was added into the water phase to give a mixture which was emulsified at 13500 rpm for 180 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1200 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 300 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 0.98% and an entrapment efficiency of 98.0%.
5.12 g of PLGA (85/15, 0.11, 7100) was weighed and dissolved in 50 ml of dichloromethane to form an oil phase, 2.4 g triptorelin acetate and 480 mg of glucose were weighed and dissolved in 5.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 17500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1300 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 300 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 26.0% and an entrapment efficiency of 86.7%.
1.90 g of PLGA (50/50, 0.23, 26000) and 100 mg of triptorelin acetate were weighed and dissolved respectively in 10 ml of dichloromethane, and 1.0 ml of water under stirring, so as to obtain clear solutions; the dissolved dichloromethane phase was added into the dissolved water phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1% PVA solution at 6° C. through an injector under homogenizing at 2100 rpm, and then was homogeneously emulsified for 2 min to obtain a double emulsion. The double emulsion was transferred to a cantilever mixer rotating at a speed of 600 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 4.49% and an entrapment efficiency of 89.8%.
Test drugs: triptorelin microspheres prepared according to Examples 5, 6, 9 and 10, which contained 1% and 5% glucose and 1% and 5% of mannitol, respectively, and a drug loading of about 4.5-4.7%.
Control group: triptorelin microspheres comprising no glucose/mannitol and a drug loading of about 4.5% as prepared according to Comparative Example 1.
Experimental animals: 20 healthy male Beagle dogs with body weights of 9-12 kg;
Test instruments: a QTRAP5500 mass spectrometer fitted with an ionspray ionization source (Applied Biosystem, Inc.);
20 healthy male Beagle dogs were divided randomly into 5 groups, including a control group (Comparative Example 1), a first experimental group (Example 5), a second experimental group (Example 6), a third experimental group (Example 9) and a fourth experimental group (Example 10), respectively, all of which were subjected to drug administration by intramuscular injection at a dose of 0.3 mg/kg, blood samples were collected before administration and 1 h, 6 h, 1 d, 2 d, 3 d, 4 d, 6 d, 9 d, 11 d, 14 d, 16 d, 19 d, 23 d, 26 d and 30 d after administration, respectively, the concentrations of triptorelin in the blood plasma of the Beagle dogs were determined by an LC-MS/MS method, and the test results were shown in Table 1 and
LC-MS/MS Method:
Liquid phase conditions: the column is Venusil MP-C18, and the mobile phase is 0.05% of acetic acid solution-methonal with the flow rate of 0.6 mL/min. The column remained at 40° C., and the injection volume is 10 μl.
Mass spectrometer conditions: the ionization source is an electro spray ionization (ESI) source; the source voltage is maintained at 5500V, and operated in positive mode; the scanner mode is multiple reaction monitoring (MRM), using the transitions of m/z 656.5-249.1 and m/z 656.5-110.1 for quantitative analysis; the declustering potential (DP) is 50V and the collision energy (CE) are 42 eV and 90 eV respectively.
The results show that the triptorelin microspheres released drugs immediately after administration, and Cmax of the triptorelin microspheres containing glucose/mannitol (i.e., glucose or mannitol) was significantly higher than those containing no glucose/mannitol. Thus, the presence of glucose/mannitol in the triptorelin microspheres was shown to increase the in vivo initial release of triptorelin as compared to triptorelin microspheres of a similar drug loading but without glucose or mannitol.
Test drugs: triptorelin microspheres prepared according to Examples 5, 6, 9 and 10, which contained 1% and 5% of glucose and 1% and 5% of mannitol, respectively, and a drug loading of about 4.5-4.7%.
Control group: triptorelin microspheres containing no release regulator and with a drug loading amount of about 4.5% prepared according to Comparative Example 1.
Test instruments: an Agilent 1290 high performance liquid chromatography system comprising a dual infusion pump, an autosampler and a column oven;
Methods: the microspheres weighed were placed in centrifuge tubes, a release medium (methanol: water=5:95) was added therein and subjected to vortex treatment for 1 min. They were then put in a water bath oscillator of 37° C.±0.5° C. for oscillation, and the centrifuge tubes were taken out after a period of 3 h, 1 d, 2 d, 3 d, 4 d, 5 d and so on, respectively, and subjected to centrifugation with a rotation speed of 3600 rpm at 5-8° C. for 15 min. The contents of triptorelin in the centrifugate were determined so as to calculate the cumulative release amounts (%), the test results were shown in Table 2 and
The in vivo and in vitro research data of Test Example 1 and Test Example 2 were subjected to Boltzmann curve fitting by the Origin software, the results were shown in Table 3.
The results show that (a) the formulations with glucose/mannitol, when compared with those without glucose/mannitol, significantly increased the in vitro initial (0-3 hours) release amount of triptorelin; (b) the in vitro initial (0-3 hours) release amount of triptorelin increased with the increase of glucose/mannitol content; (c) the in vitro and in vivo release data obtained by an in vitro assay method had a good correlation, with all R values being above 0.9 (Table 3).
Test drugs: triptorelin microspheres prepared according to Examples 5, 6, 9 and 10, which contained 1% and 5% of glucose and 1% and 5% of mannitol, respectively, and a drug loading of about 4.5-4.7%;
Control group: triptorelin microspheres containing no release regulator and with a drug loading amount of about 4.5% prepared according to Comparative Example 1;
Negative (solvent) control group: 1% sodium carboxymethyl cellulose, 2 ml per vial;
Rat serum hormone detection kit: rat testosterone (T) ELISA kit, from R&D systems, Inc.
Experimental animals: 56 male rats with body weights of 200-250 g; Test instruments: a high-speed refrigerated centrifuge (Beckman Coulter, Inc., Allegra X-22R);
56 healthy male rats were divided randomly into 7 groups, including a castrated group, a negative control group, a control group (Comparative Example 1), a first experimental group (Example 5), a second experimental group (Example 6), a third experimental group (Example 9) and a fourth experimental group (Example 10), respectively, and all of which were subjected to intramuscular injection administration at a dose of 300 μg/kg, with the rats of the castrated group being castrated on the day of administration, and blood samples were collected from left and right eye sockets alternately before administration and 1 d, 4 d, 7 d, 10 d, 14 d, 18 d, 21 d, 25 d, 28 d, 32 d and 35 d after administration, respectively, with the blood sampling time at 8:00 to 10:00 in the morning. The blood samples were stood still at room temperature for 1 h, and then were centrifuged at 1000 g/min for 20 min to give supernatants, and the concentrations of serum testosterone were detected by an ELISA kit, the results were shown in Table 4 and
The results show that a) the testosterone level of those groups administrated with the triptorelin microspheres without glucose or mannitol decreased to a castration level, i.e. began acting, on the 10th to 14th days; while the triptorelin microspheres containing glucose/mannitol began acting on the 4th day. Therefore, the triptorelin microspheres comprising glucose/mannitol were able to act faster;
b) all the testosterone concentrations of those groups administrated with the microspheres comprising glucose were kept steady at the castration level from the 4th day to the 28th day; while the testosterone concentrations of those groups administrated with the microspheres comprising mannitol were substantially kept at the castration level from the 4th day to the 21th day, but fluctuated around the 14th day. Therefore, compared to mannitol, glucose was able to maintain the pharmaceutical effects for a longer period, with more steady pharmaceutical effects over the period of release.
1.798 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 8 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 2 mg of glucose were weighed and dissolved in 0.8 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 2000 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 500 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.13% and an entrapment efficiency of 91.3%.
1.78 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 8 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 20 mg of glucose were weighed and dissolved in 0.8 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 2000 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 500 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.01% and an entrapment efficiency of 90.1%.
1.60 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 200 mg of glucose were weighed and dissolved in 1.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 17500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1800 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 300 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.24% and an entrapment efficiency of 92.4%.
1.798 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 8 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 2 mg of mannitol were weighed and dissolved in 0.8 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 2000 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 500 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.12% and an entrapment efficiency of 91.2%.
1.78 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 8 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 20 mg of mannitol were weighed and dissolved in 0.8 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 2000 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 500 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 8.95% and an entrapment efficiency of 89.5%.
1.60 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 200 mg of mannitol were weighed and dissolved in 1.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 17500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1800 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 400 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 8.98% and an entrapment efficiency of 89.8%.
1.79 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 10 mg of glucose were weighed and dissolved in 5.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 2200 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 400 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.22% and an entrapment efficiency of 92.2%.
1.79 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate and 10 mg of mannitol were weighed and dissolved in 1.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 2200 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 400 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.15% and an entrapment efficiency of 91.5%.
1.80 g of PLGA (50/50, 0.25, 26000) was weighed and dissolved in 10 ml of dichloromethane to form an oil phase, 200 mg of triptorelin acetate was weighed and dissolved in 1.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 15000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 1000 ml of a 1% PVA solution at 8° C. through an injector under homogenizing at 2000 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 500 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 9.13% and an entrapment efficiency of 91.3%.
Test method: the same as that in Test Example 2.
Test Materials:
Test drugs: triptorelin microspheres prepared according to Example 14-19.
Control group: triptorelin microspheres without glucose/mannitol as prepared according to Comparative Example 2.
The test results were shown in Table 5 and
The results show that (a) the formulations with glucose/mannitol, when compared with those without glucose/mannitol, significantly increased the in vitro initial (0-3 hours) release amount of triptorelin; (b) the in vitro initial (0-3 hours) release amount of the microspheres increased with the increase of the glucose/mannitol content.
Test method: the same as that in Test Example 3.
Test drugs: triptorelin microspheres prepared according to Example 15-16, 18-21.
Control group: triptorelin microspheres without glucose/mannitol as prepared according to Comparative Example 2.
The test results were shown in Table 6 and
The results show that a) the testosterone level of those groups administrated with the triptorelin microspheres without glucose or mannitol decreased to a castration level, i.e. began acting, on the 10th to 14th days; while the triptorelin microspheres containing glucose/mannitol began acting on the 4th day. Therefore, the triptorelin microspheres comprising glucose/mannitol were able to act faster;
b) all the testosterone concentrations of those groups administrated with the microspheres comprising glucose were kept steady at the castration level from the 4th day to the 28th day; while the testosterone concentrations of those groups administrated with the microspheres comprising mannitol were substantially kept at the castration level from the 4th day to the 21th day, but fluctuated around the 14th day. Therefore, as compared to mannitol, glucose was able to maintain a longer period and more steady pharmaceutical effects.
5.592 g of PLGA (75/25, 0.51, 70000) was weighed and dissolved in 40 ml of dichloromethane to form an oil phase, 2.4 g of triptorelin acetate and 8 mg of glucose were weighed and dissolved in 4.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1300 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 350 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 26.37% and an entrapment efficiency of 87.9%.
5.56 g of PLGA (75/25, 0.51, 70000) was weighed and dissolved in 50 ml of dichloromethane to form an oil phase, 2.4 g of triptorelin acetate and 40 mg of glucose were weighed and dissolved in 5.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1300 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 350 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 26.46% and an entrapment efficiency of 88.2%.
4.8 g of PLGA (75/25, 0.51, 70000) was weighed and dissolved in 50 ml of dichloromethane to form an oil phase, 2.4 g of triptorelin acetate and 800 mg of glucose were weighed and dissolved in 5.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1300 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 350 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 27.42% and an entrapment efficiency of 91.4%.
5.592 g of PLGA (75/25, 0.51, 70000) was weighed and dissolved in 40 ml of dichloromethane to form an oil phase, 2.4 g of triptorelin acetate and 8 mg of mannitol were weighed and dissolved in 4.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1300 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 350 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 26.82% and an entrapment efficiency of 89.4%.
5.56 g of PLGA (75/25, 0.51, 70000) was weighed and dissolved in 50 ml of dichloromethane to form an oil phase, 2.4 g of triptorelin acetate and 40 mg of mannitol were weighed and dissolved in 5.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 12000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1500 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 300 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 27.15% and an entrapment efficiency of 90.5%.
4.8 g of PLGA (75/25, 0.51, 70000) was weighed and dissolved in 50 ml of dichloromethane to form an oil phase, 2.4 g of triptorelin acetate and 800 mg of mannitol were weighed and dissolved in 5.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 12000 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1.0% PVA solution at 8° C. through an injector under homogenizing at 1500 rpm, and then it was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 300 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 27.84% and an entrapment efficiency of 92.8%.
5.6 g of PLGA (75/25, 0.51, 70000) was weighed and dissolved in 50 ml of dichloromethane to form an oil phase, 2.4 mg of triptorelin acetate was weighed and dissolved in 5.0 ml of water to form a water phase; and then the water phase was added into the oil phase to give a mixture which was emulsified at 13500 rpm for 90 s to obtain a primary emulsion. The primary emulsion was added into 4000 ml of a 1% PVA solution at 8° C. through an injector under homogenizing at 1300 rpm, and then was homogeneously emulsified for 3 min to obtain a double emulsion. The homogenized double emulsion was transferred to a cantilever mixer rotating at a speed of 350 rpm, and was stirred for 5 h to volatilize and remove the organic solvent; and the residue was filtered by a screen, washed by deionized water, and freeze-dried to obtain powdery microspheres. The microspheres had a drug loading amount of 27.5% and an entrapment efficiency of 91.7%.
Test method: the same as that in Test Example 2.
Test Materials:
Test drugs: triptorelin microspheres prepared according to Example 22, 24, 25, and 27.
Control group: triptorelin microspheres without glucose/mannitol prepared according to Comparative Example 3.
The test results were shown in Table 7 and
The results show that (a) the formulations with glucose/mannitol, when compared with those without glucose/mannitol, significantly increased the in vitro initial (0-3 hours) release amount of triptorelin; (b) the in vitro initial (0-3 hours) release amount of triptorelin increased with the increase of the glucose/mannitol content.
Test method: the same as that in Test Example 3.
Test drugs: triptorelin microspheres prepared according to Example 23-24, 26-27.
Control group: triptorelin microspheres without glucose/mannitol prepared according to Comparative Example 3.
The test results were shown in Table 8 and
The results show that a) the testosterone level of those groups administrated with the triptorelin microspheres without glucose or mannitol was decreased to a castration level, i.e. began acting, on the 10th to 14th days, while the triptorelin microspheres containing glucose/mannitol began acting on the 4th day. Therefore, the triptorelin microspheres comprising glucose/mannitol were able to act faster;
b) all the testosterone concentrations of those groups administrated with the microspheres comprising glucose were kept steady at the castration level from the 4th day to the 84th day, while the testosterone concentrations of those groups administrated with the microspheres comprising mannitol were substantially kept at the castration level from the 4th day to the 70th day, but fluctuated around the 35th day, therefore, compared to mannitol, glucose was able to maintain a longer period and more steady pharmaceutical effects.
| Number | Date | Country | Kind |
|---|---|---|---|
| 201110435894.3 | Dec 2011 | CN | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/CN2012/001712 | 12/18/2012 | WO | 00 | 6/19/2014 |
