KR101562369B1 - pH sensitive lipopeptide containing composite of polyhistidine and phospholipid, and process for preparing the same - Google Patents

Abstract

The present invention relates to a pH-sensitive lipid peptide containing a combination of polyhistidine and a phospholipid. Since the lipid peptide according to the present invention contains a combination of polyhistidine and phospholipid, various drugs are loaded to slowly release the drug over time, and exhibits high cytotoxicity in a weakly acidic environment due to pH sensitivity, And can be usefully used as a drug delivery vehicle for a specific disease that acts efficiently and has environmental changes of weakly acidic conditions. In particular, it can specifically act on cancer cells and tumors, and thus can be usefully used as an anticancer agent.

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a pH sensitive lipid peptide containing polyhistidine and a phospholipid conjugate, and a pH sensitive lipopeptide containing composite of polyhistidine and phospholipid,

The present invention relates to a pH-sensitive lipid peptide containing a conjugate of a polyhistidine and a phospholipid, a method for producing the same, and a drug delivery system containing the same.

Although many drugs are effective in dosing more than the amount needed to produce a drug efficacy appropriate to the site of the disease, they can cause side effects in other parts due to the inappropriate amount of the drug. This has led many pharmaceutical companies to have a need for formulations that reduce these side effects and maximize their efficacy.

In order to solve the above problems, the drug delivery system (hereinafter referred to as DDS) has been increasingly utilized. The DDS is a method of maximizing the efficacy and effectiveness by minimizing side effects of existing medicines. It is useful for improving the selectivity of drugs which are difficult to administer. The use of special delivery systems is required if the drug being administered exhibits physico-chemical or pharmacokinetic specific properties such as high water solubility, high fat solubility, insolubility, and the like.

In addition, drugs with special requirements, such as toxic single dose injectable drugs, cytotoxic unstable drugs, high clearance drugs, readily inactivated drugs in vivo, topical application The required drugs, etc. should be considered to have the appropriate DDS. The DDS technology has been actively researched since the 1970s by advanced countries in advanced technology. Since the introduction of the substance patent system in 1987, domestic drug companies who have felt a sense of crisis have developed a new drug product that applies the DDS, which improves the disadvantages of the existing drugs rather than the development of the new drugs that cost an average of 15 years and costs over $ 200 million. We found that the time and cost required for development was shortened to about one third and the probability of success was very high. In Korea, full-scale research has been started since 1990, and related patent applications have been steadily increasing since 1992.

Biocompatible polymers are used in place of various medical practices and body parts including DDS technology and diagnosis and treatment. Recently, studies on drug delivery systems using such biocompatible polymers have been actively conducted. Oral administration, which is the most convenient method for drug delivery, has been the most preferred because it can relieve the pain of injection administration. Emulsion, nano particles, and liposomes are widely used as drug delivery systems for oral administration. Among them, liposomes made of phospholipids existing in biological membranes are widely used as drug delivery agents because they have excellent biocompatibility, biodegradability, and reduced toxicity. Previously, the in vivo circulation time of the encapsulated drug in PEG-conjugated liposomes was significantly increased and thus had more opportunities to be absorbed into the tumor via the EPR effect. Nevertheless, PEGylation seriously interferes with liposome uptake into tumor cells. To overcome this problem, conjugation of PEG to the surface of liposomes via pH-sensitive, MMP-sensitive, esterase-sensitive or reduced-potential-sensitive chemical bonding and the subsequent dissociation of PEG out of the cell Is being reported.

The biggest problem of chemotherapy using existing anticancer drugs was that cancer drugs killed not only cancer cells but also normal cells, causing severe damage to the human body. However, since nanoparticles such as micelles and liposomes are very small, ranging from several tens to several hundred nanometers, they can be injected into the human body, easily recognize and absorb the cells, move along the blood vessels in the human body, By gradually releasing the anticancer drug which is contained in the cancer cell while staying relatively long around the cancer cell relatively poorly through the vascular hole formed around the cancer cell by the development, it can prevent the destruction of the normal cell distributed around the cancer cell, (H. Maeda, et al., Bioconjugate Chem. 3 (1992) 351-362; RK Jain, Adv. Drug Deliv. Rev. 46 (2001) 149168).

In addition, it is generally known that the pH of normal tissues and blood is 7.4, while the pH of cancer cells is between 7.0-6.5 on average. Therefore, when attention is paid to the fact that most of the solid cancer cells have a weak acidic pH around the cells, the development of a pH-sensitive polymer material capable of concentrating the pH of the cancer cells can be widely used for diagnosis and treatment of cancer, Is likely to be used as a material for the development of medicines for the diagnosis and treatment of weakly acidic lesions and rheumatoid arthritis.

Accordingly, the present inventors have made efforts to produce a novel drug delivery system using lipid peptides. As a result, they have produced a lipid peptide having a phospholipid and a poly (histidine) (poly (His)) as a pH sensitive polypeptide. And thus the present invention has been completed.

The present invention provides a pH-sensitive lipid peptide containing a conjugate of polyhistidine and a phospholipid, and a method for producing the same.

It is another object of the present invention to provide a drug delivery system comprising the pH-sensitive lipid peptide.

The present invention provides a pH-sensitive lipid peptide containing a conjugate of a polyhistidine and a phospholipid and a method for producing the same.

The present invention also provides a drug delivery system comprising the pH-sensitive lipid peptide.

Since the lipid peptide according to the present invention contains a combination of polyhistidine and phospholipid, various drugs are loaded to slowly release the drug over time, and exhibits high cytotoxicity in a weakly acidic environment due to pH sensitivity, And can be usefully used as a drug delivery vehicle for a specific disease that acts efficiently and has environmental changes of weakly acidic conditions. In particular, it can specifically act on cancer cells and tumors, and thus can be usefully used as an anticancer agent.

1 is a photograph showing DPPE-p (His) _n of the present invention with a near-infrared fluorescent probe.
Fig. 2 is a diagram showing the in vitro release profile of doxorubicin over time in DPPE-p (His) _n micelles loaded with doxorubicin.
FIG. 3 is a graph showing cell activity according to pH change when DPPE-p (His) _n micelles (a, b) and doxorubicin (c) loaded with doxorubicin are treated.
FIG. 4 shows the results of confirmation of intracellularization of DPPE-p (His) _n micelles loaded with doxorubicin through confocal microscopy.
Fig. 5 is a graph showing the results of flow cytometric analysis of the cellular internalization of DPPE-p (His) _n micelle loaded with doxorubicin.
FIG. 6 is a graph showing the results of NIR imaging of the drug delivery effect of intravenous injection of DPPE-p (His) _n micellar solution loaded with doxorubicin in a mouse.
FIG. 7 shows (a) and (b) graphs showing the effect of drug delivery on the organs of mice when the solution of DPPE-p (His) _n micelle loaded with doxorubicin was intravenously injected into mice through white light and NIR images, Fig.

The present invention provides a pH-sensitive lipid peptide containing a combination of polyhistidine and a phospholipid.

Hereinafter, the present invention will be described in more detail.

The lipid peptide of the present invention is characterized in that it is contained in the form of a conjugate in which a histidine and a phospholipid are combined in order to exhibit pH sensitivity, which exhibits a swelling property when the acidity of the polypeptide is lowered.

Histidine is well tolerated in acidic conditions and is suitable for weakly acidic conditions. Poly (His) exhibits biocompatibility and biodegradability due to the proton sponge mechanism of imidazole group and has excellent effect on membrane degradation during endosomal fusion control .

Examples of the phospholipid include distearoyl-sn-Gylcero-3-phosphatidylethanolamine (DSPE), dipalmitoyl phosphatidylethanol amine (DPPE), phosphatidylethanol amine (PPEA) Phosphatidylserine (PPS), phosphatidyl glycerol (PPG), phosphatidylcholine (PPC), dipalmitoyl phosphatidylserine (DPPS), dipalmitoyl phosphatidyl glycerol (DPPG) ) And dipalmitoyl phosphatidylcholine (DPPC), but it is not limited thereto, and it is most preferable to use a pH sensitive material such as dipalmitoyl phosphatidylethanolamine (DPPE).

The lipid peptide according to the present invention may be DPPE-p (His) wherein DPPE represented by the following formula (1) is combined with polyhistidine.

[Chemical Formula 1]

In Formula 1, n is an integer of 25 to 100.

In addition,

(a) introducing a benzyl protecting group to the histidine;

step (b) was added and the polymerization solution to the phospholipid -NH ₂ the benzyl protecting group is introduced to obtain a phospholipid-histidine -p (Bn-His) _n; And

(c) adding an excessive acidic solution to the phospholipid-p (Bn-His) _n and stirring to obtain a deprotected phospholipid-p (His) _n . do.

The process for preparing the pH-sensitive lipid peptide according to the present invention will be described in detail as follows.

The step (a) is a step of introducing a benzyl protecting group into histidine, wherein PCl ₅ and Boc-L-His (Bn) -OH are reacted in dioxane to prepare a histidine having a benzyl protecting group introduced therein.

The step (b) is a step of binding the phospholipid with histidine, which is performed under a nitrogen atmosphere. The reaction proceeds through ring opening polymerization (ROP) of histidine incorporating the benzyl protecting group initiated by the primary amino group. That is, the polymerization proceeds at 15 to 35 ° C for 60 to 90 hours, preferably at 25 ° C for 72 hours. After the polymerization reaction, the solvent is concentrated and the concentrated solution is precipitated and dried to obtain phospholipid-p (Bn-His) _n .

The step (c) is a step of deprotecting the benzyl protecting group. The phospholipid-p (Bn-His) _n is dissolved in trifluoroacetic acid, and an excess amount thereof, preferably 3 to 5 times, A 4-fold molar amount of an acidic solution is added. At this time, HBr solution, HCl solution, H ₂ SO ₄ solution and the like may be used as the acid solution, but it is not limited thereto. The reaction solution is stirred at 20 to 40 ° C for 10 to 20 hours, preferably at 30 ° C for 16 hours to prepare a deprotected phospholipid-p (Bn-His) _n with a benzyl protecting group.

The present invention also provides a drug delivery system comprising a lipid peptide containing a drug-loaded conjugate of polyhistidine and a phospholipid.

The loadable drug may include an anti-cancer agent, an antiviral agent, steroidal antiinflammatory drugs, an antibiotic, an antifungal agent, an anesthetic agent, an analgesic agent, an anabolic steroid agent, an immunosuppressant agent and an immunostimulating agent.

Examples of the anticancer agent include paclitaxel, methotrexate, doxorubicin, 5-fluorouracil, mitomycin-C, styrene maleic acid neocarzinostatin ( Such as styrene maleic acid neocarzinostatin (SMANCS), cisplatin, carboplatin, carmustine (BCNU), dacabazine, etoposide and daunomycin. .

A representative structure of the drug delivery system according to the present invention can be represented by the following formula (2).

(2)

Formula 2 represents a conjugate of polyhistidine and DPPE loaded with doxorubicin.

The lipid peptide loaded with various drugs including the anticancer agent according to the present invention slowly releases the drug over time and exhibits high cytotoxicity due to pH sensitivity in a weakly acidic environment and acts selectively and efficiently on weakly acidic cells, Can be usefully used as a drug delivery vehicle for a specific disease having an environmental change of < RTI ID = 0.0 > In particular, it can specifically act on cancer cells and tumors, and thus can be usefully used as an anticancer agent.

It will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the spirit or scope of the invention as defined by the appended claims. It will be obvious to you.

Example 1. Synthesis of 1,2-dipalmitoyl-sn-glycero-3-phosphoethanolamine-poly (L-histidine) _n (1,2-dipalmitoyl-sn-glycero-3-phosphoethanolamine-poly (L-Histidine) _n ) [DPPE-p (His) _n ]

All reagents and solvents were purchased from commercial suppliers and generally accepted unless otherwise specified. (99%), triethylamine (TEA, 99.5%), Doxorubicin hydrochloride (Dox, 98.5%), IR-820 dye (80% dye content), N N-hydroxy succinimide (NHS, 99%) and dicyclohexyl carbodimide (DCC, 99%) were purchased from Sigma-Aldrich Co. (USA) . 1,2-Dipalmitoyl-sn-glycero-3-phosphoethanolamine (DPPE, 99%) was purchased from avanti polar lipids. N-α-t-butyloxycarbonyl-N-im-benzyl-L-histidine (Boc-L-His- (Bzl) - OH) were purchased from Bachem. N, N-dimethylformamide (DMF), dichloromethane, diethyl ether and n-hexane were distilled with sodium hydride and calcium, respectively. 1,4-dioxane was purified by column chromatography with active Al2O3 to remove impurities mixed with impurities and then distilled. All other chemical reagents were purchased from TCI and used without further purification.

1-1. Preparation of benzyl-N-carboxy-L-histidine anhydride [Bn-His-NCA]

Boc-L-His (Bn) -OH (2.5 g) was added to 10 mL of a solution containing 1.8 g of PCl _{5 in} 20 mL of 1,4-dioxane to prepare Bn-His- 0.0 > 25 C < / RTI > with stirring. Within a few minutes, a clear solution filtered through a glass filter was obtained. The filtrate was added to an excessive amount of diethyl ether to obtain crystals of Bn-His-NCA. The product was then rinsed and dried at 50 [deg.] C in vacuo.

1-2. Glycero-3-phosphoethanolamine-benzyl-N-carboxy-L-histidine anhydride (1,2-dipalmitoyl-sn-glycero-3-phosphoethanolamine-benzyl-N-carboxy -L-histidine anhydride [DPPE-p (Bn-His) _n ]

After the addition of DPPE-NH ₂ of 0.68g (0.36mmoL) in a nitrogen atmosphere to a shrink tube (schlenk tube) of the nitrogen is removed, dried over anhydrous DMF / chloroform of 5mL (3: 2) was added to the lipid initiator ( lipid initiator. A 5 mL DMF solution containing a predetermined amount of Bn-His-NCA the transfer needle (transfer needle) was used and added to DPPE-NH ₂ solution under a nitrogen atmosphere. The mixture was reacted under nitrogen atmosphere at room temperature for 72 hours. After the polymerization reaction, the solvent was concentrated under high vacuum. The concentrated reaction solution was precipitated in cold diethyl ether and dried in vacuo to give DPPE-p (Bn-His) _n (n = 10, 25, 50, 100).

1-3. Dipalmitoyl-sn-glycero-3-phosphoethanolamine-poly (L-histidine) _n (1,2-dipalmitoyl-sn-glycero-3-phosphoethanolamine-poly (L-Histidine) _n ) [DPPE-p (His) _n ]

To remove the benzyl protecting group, a solution of DPPE-p (Bn-His) _{n in} trifluoroacetic acid (100 mg, 10 mL) was placed in a round bottom flask. A 4-fold molar amount of a 33 wt% solution of HBr in acetic acid was then added and the reaction mixture was stirred at 30 < 0 > C for 16 h. Finally, the reaction mixture was precipitated in cold diethyl ether to give DPPE-p (His) _n (n = 10, 25, 50, 100). The resulting pale yellow solid was redissolved in 10 mL of DMF and further purified by bulk dialysis with deionized water. The water was removed by freeze-drying to give the product as a white solid (70% yield).

The prepared DPPE-p (Bn-His) _n was confirmed by a near-infrared fluorescent probe, and it is shown in Fig.

Example 2. Preparation of micelles loaded with doxorubicin

2-1. Preparation of aminocaproic acid conjugated with IR-820 dye

IR-820 dye (150 mg, 0.17 mmol) and 6-aminocaproic acid (30 mg, 0.23 mmol) were added to 5 mL of DMF followed by 30 μL of TEA (22 mg, 0.17 mmol). The reaction solution was heated at 70 占 폚 and stirred under dark condition for 12 hours. The solvent was removed in vacuo and the resulting dark blue solid was rinsed with ether and further purified by column chromatography with gradient elution from ethyl acetate to ethyl acetate / methanol (5: 1). After removal of the solvent in vacuo, a dark blue solid product was obtained (52% yield).

2-2. Preparation of NIRF prodrug DPPE-p (His)

After dissolving aminocaproic acid coupled with IR-820 dye (5.0 mg, 5.1 mmol) in 1 mL of DMF solution, 1 mL of DMF containing 0.69 mg of HOSu (6.0 mmol) and 1.5 mg DCC (7.3 mmol) was added Respectively. The reaction mixture was stirred at room temperature for 24 hours under dark conditions. DPPE-p (His) (30 mg, 4.6 mmol) was added to DMF, and 90 μL of the dye solution was added dropwise while stirring. The mixed solution was stirred overnight and then precipitated in cold ether to isolate the NIRF prodrug. A DMF solution of the NIRF prodrug was further purified by dialysis under dark conditions. Water was removed by freeze-drying after dialysis to give the product as a gray solid (72% yield).

2-3 . DPPE-p (His) _n  Preparation of lipopeptide micelles

All procedures were performed under dark conditions. DPPE-p (His) _n lipopeptide micelles were prepared by self-assembly as follows. Specifically, 10 mg of DPPE-p (His) _n was dissolved in 5 mL of DMF and 3 mL of deionized water was added to the polymer solution with very slow stirring. The solution was then heated to < RTI ID = 0.0 > 60 C < / RTI > The resulting turbid solution was then transferred to a dialysis tube (Spectra / Por, MWCO = 3000) and dialyzed with deionized water for 48 hours with frequent water changes. The micelle suspension thus obtained was filtered using a 0.45 nm membrane filter (Millipore).

2-4. Preparation of micelles loaded with doxorubicin

Doxorubicin HCl was stirred with excess TEA (1.2 x DOX.HCl) in DMSO overnight to obtain doxorubicin base. The NIRF prodrug DPPE-p (His) ₇₅ (80 mg) was dissolved in DMSO (5 mL) in a glass vial, mixed with doxorubicin base solution (20 mg doxorubicin in 3 mL DMSO) and stirred for 1 hour. The reaction solution was added dropwise to deionized water (10 mL). The reaction solution was then transferred to a dialysis tube (Spectra / Por, MWCO = 3000) and dialyzed with deionized water at room temperature for 36 hours with frequent water changes. The mixture in the dialysis tube was then filtered through a 0.45 nm syringe filter (Millipore) to remove doxorubicin aggregates. The micellar solution loaded with doxorubicin was collected and kept at 4 ° C. Average particle size, size distribution and morphology of micelles loaded with micelles and doxorubicin were measured by dynamic light scattering and transmission electron microscopy.

2-5. Measurements of drug loading, drug loading efficiency, and in vitro release profile of doxorubicin in micelles loaded with doxorubicin

The drug loading and drug loading efficiencies were determined by ultraviolet spectroscopy (excitation at 485 nm) in DMSO using a calibration curve obtained from doxorubicin / DMSO solutions with different concentrations of doxorubicin. Drug loading (DLC) and drug loading efficiency (DLE) were calculated according to the following formula:

Drug loading (DLC) (wt%) = [weight of loaded drug / weight of drug-bound micelle] x 100%

Drug Loading Efficiency (DLE) (wt%) = [Weight of drug loaded / Weight of drug administered] × 100%

5 mL of micellar suspension (containing 2.35 mg of doxorubicin conjugated micelle, 17 wt% of DLC, 400 mg of doxorubicin) was dialyzed against 30 mL of PBS buffer (Spectra / Por, MWCO 3000). At certain time intervals, 2 mL medium outside the dialysis tubing was periodically removed and replaced with fresh PBS buffer solution. The concentration of doxorubicin was calculated based on the absorption intensity at 485 nm using ultraviolet visible spectroscopy.

The in vitro release profile of doxorubicin in the drug loaded micelles was observed by dialysis of micellar suspension conjugated with doxorubicin in PBS buffer solution at pH 7.4 and 5.5, and the observation results are shown in FIG.

As shown in FIG. 2, it was confirmed that the amount of doxorubicin released from micelles increases with time.

Experimental Example 1. Preparation of DPPE-p (His) _n  Cytotoxicity analysis of micelles

Human embryonic kidney 293T cells, human colon cancer (HCT) -116 cells, and human breast cancer (MCF7) normal cells were used to assess the cytotoxicity of nano-sized micelles of DPPE-p (His) _n . Specifically, 1 × 10 ⁶ cells were inoculated into 96-well plates with 100 μL of RPMI 1640 and 10% FBS and incubated at 37 ° C. and 5% CO ₂ overnight. DPPE-p (His) _n micelles dissolved in DMSO were diluted 100-fold in serum-free media and then added to the cells. Control groups were treated with 1% DMSO. After 2 days, viable cells were measured by MTT cell proliferation assay. 30 [mu] L of MTT (5 mg / mL) was added to the 96-well plate and further incubated in the CO ₂ incubator for 4 hours. The formazan crystals formed in the cells were dissolved in SDS solution (100 μl of SDS-HCl solution (SDS 10% w / v, 0.01M HCl)) and the absorbance (560 nm sample / 630 nm standard) was automatically measured using a computer-connected microplate reader (Molecular Device Company, Sunnyvale, Calif.). Each treatment was averaged in 8 wells. The results show the absorbance in the drug treated cells as a percentage compared to the absorbance in the control cells, which is shown in FIG. FIG. 3A shows the case of treating DPPE-p (His) _n loaded with doxorubicin, and FIG. 3B shows the case of treating only doxorubicin.

As shown in Fig. 3, when (a, b) DPPE-p (His) _n loaded with doxorubicin was treated, the cell activity was inferior in weak acidity and it was confirmed that cytotoxicity was low in weak acidity. (c) It was confirmed that cytotoxicity was not high in weak acidity.

Experimental Example 2: Preparation of DPPE-p (His) _n In vitro anti-cancer effect

The anti-cancer effects of doxorubicin-loaded DPPE-p (His) _n micelles and doxorubicin-free micelles were evaluated with MCF 7 human breast cancer cell lines. Specifically, 3 × 10 ⁴ MCF 7 cells were inoculated into 96-well plates with 100 μL of RPMI 1640 and 10% FBS and incubated overnight at 37 ° C. and 5% CO ₂ in the atmosphere for 24 hours. The medium was then treated with DPPE-p (His) _n micelles loaded with doxorubicin or doxorubicin in serum-free medium at the required pH. After 24 hours, viable cells were evaluated by MTT cell proliferation assay as described in Experimental Example 1 above.

The cellular internalization of DPPE-p (His) _n micelles loaded with doxorubicin was confirmed by confocal microscopy and flow cytometer analysis. MCF 7 cells were inoculated into 6-well plates with cover-glass and cultured in a CO ₂ incubator for 12 hours. Then doxorubicin or DPPE-p (His) _n micelles in serum-free medium were treated with MCF 7 cells for 1 hour at the required pH. The cells were then rinsed with PBS (pH 7.4, 0.1 M) and treated with 4% paraformaldehyde. Cells were then washed again with PBS and fixed with immobilization solution (ImmuMount, Thermo Electron Corporation, Pittsburgh, Pa.). The cells were observed with a confocal laser scanning microscope (CLSM, TCS-SP2; Leica, Wetzlar, Germany) and the results are shown in FIG.

For flow cytometry, micelles loaded with doxorubicin or doxorubicin treated with MCF 7 (1 × 10 ⁶ ) cells were inoculated into 6-well plates and incubated with 1 μg of doxorubicin-free or doxorubicin-conjugated nanoparticles at different pH Lt; / RTI > Cells were then washed with PBS and harvested by centrifugation. The fluorescence intensity of the cells was measured with a flow cytometer, and the measurement results are shown in Fig.

(Request a brief description of Figures 4 and 5)

Experimental Example 3 DPPE-p (His) with doxorubicin in mice _n Administration Anti-cancer effect measurement

All animals were maintained in accordance with the guidelines outlined in the instructions for the management and use of laboratory animals approved by the Laboratory Animal Use and Management Committee at Pusan National University. Animal experiments were performed using female BALB / c nude mice (age: 5 weeks, weight: 18-22 g). MCF7 cancer cells (1 x 10 ⁶ cells / mouse) were subcutaneously administered to mice and the like. A tumor transplantation mouse with a tumor volume of 3 mm x 3 mm was used, and a micelle solution containing 100 mL of doxorubicin was intravenously injected through the tail vein of a mouse.

Mice were divided into four groups as follows:

(1) a control group injected with PBS (phosphate buffered saline); (2) a group treated only with doxorubicin (doxorubicin dissolved in PBS and then injected with a mouse); (3) empty micelle treatment group (DPPE-p (His) ₅₀ micelles are dispersed in deionized water and then injected); (4) a micelle treatment group in which doxorubicin is loaded (micelle loaded with doxorubicin is injected into each mouse).

The dosing dose of doxorubicin was 5 mg per kg of mice. All groups consisted of five ear-transplanted mice transplanted in the ear, and these mice were followed up individually during the entire study period. Tumor size changes were recorded, and the tumor volume was then calculated by the following formula: Tumor volume (mm ³ ) = (length x width ² ) / 2.

The drug delivery effect of the mice injected with the micelles loaded with doxorubicin of the above (4) group over time was confirmed by NIR (Near Infrared) imaging, and the results are shown in FIG.

As shown in Fig. 6, after 24 hours, it was confirmed that the micelles loaded with doxorubicin migrated to the tumor and continued to act specifically on the tumor even after 72 hours.

In addition, DPPE-p (His) ₅₀ micelles were intravenously injected into mice, and then the organs were collected from the incised mice to confirm the drug delivery effect. The results are shown in FIG. FIG. 7A is a view through white light and NIR image, and FIG. 7B is a graph thereof.

As shown in Fig. 7, it was confirmed that the micelles loaded with doxorubicin exclusively acted on only weakly acidic tumors.

Claims (9)

A pH-sensitive lipid peptide comprising a conjugate of a polyhistidine and a phospholipid represented by the following formula (1).
[Chemical Formula 1]

In Formula 1, n is an integer of 25 to 100. The pH-sensitive lipid peptide according to claim 1, wherein the phospholipid is dipalmitoyl-glycero-phosphoethanolamine (DPPE). (a) introducing a benzyl protecting group to the histidine;
step (b) was added and the polymerization solution to the phospholipid -NH ₂ the benzyl protecting group is introduced to obtain a phospholipid-histidine -p (Bn-His) _n; And
(c) adding an excessive acidic solution to the phospholipid-p (Bn-His) _n and stirring to obtain a deprotected phospholipid-p (His) _n . 4. The method according to claim 3, wherein the acidic solution in step (c) is at least one selected from the group consisting of HBr solution, HCl solution and H ₂ SO ₄ solution. A drug delivery system comprising a pH-sensitive lipid peptide according to claim 1 or 2, wherein the drug is loaded. 6. The method of claim 5, wherein the drug is at least one selected from the group consisting of an anti-cancer agent, an antiviral agent, steroidal antiinflammatory drugs, an antibiotic, an antifungal agent, an anesthetic agent, an analgesic agent, an anabolic steroid agent, Characterized by a drug delivery system. The method of claim 6, wherein the anticancer agent is selected from the group consisting of paclitaxel, methotrexate, doxorubicin, 5-fluorouracil, mitomycin-C, But are not limited to, styrene maleic acid neocarzinostatin (SMANCS), cisplatin, carboplatin, carmustine (BCNU), dacabazine, etoposide, Wherein the drug delivery system is at least one selected from the group consisting of daunomycin. delete delete

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