CN115089759A - Polylactic acid-based polyester hemostatic sponge and preparation method and application thereof - Google Patents
Polylactic acid-based polyester hemostatic sponge and preparation method and application thereof Download PDFInfo
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- CN115089759A CN115089759A CN202210899664.0A CN202210899664A CN115089759A CN 115089759 A CN115089759 A CN 115089759A CN 202210899664 A CN202210899664 A CN 202210899664A CN 115089759 A CN115089759 A CN 115089759A
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
- A61L24/06—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials obtained by reactions only involving carbon-to-carbon unsaturated bonds
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/001—Use of materials characterised by their function or physical properties
- A61L24/0036—Porous materials, e.g. foams or sponges
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/001—Use of materials characterised by their function or physical properties
- A61L24/0042—Materials resorbable by the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2400/00—Materials characterised by their function or physical properties
- A61L2400/04—Materials for stopping bleeding
Abstract
The invention provides a polylactic acid (PLA) based polyester hemostatic sponge, which is prepared by mixing a polylactide-glycolide copolymer (PLGA) and a polylactide-caprolactone copolymer (PLCL). The PLGA comprises one or two of unmodified PLGA and end group modified PLGA; the end group modified PLGA is PLGA modified by one or more of amino, aldehyde and carboxyl. The sponge prepared by the invention has uniform pore distribution and adjustable porosity, water absorption and the like, namely, the pore diameter, the water absorption property, the hemostatic capacity and other properties of the polylactic acid-based polyester hemostatic sponge are adjusted by changing the proportion of Lactide (LA) and Glycolide (GA) in PLGA and the proportion of LA and caprolactone (GA) in PLCL, thereby realizing the hemostatic effect on different types of wound surfaces.
Description
Technical Field
The invention relates to the technical field, in particular to a polylactic acid-based polyester hemostatic sponge and a preparation method and application thereof.
Background
In war, traffic accident, surgery and various emergency incidents, massive blood loss is one of the leading causes of death. Effective hemostasis is a key step of emergency medical treatment and cure and is also a key for improving the survival rate of the injured person, so that research and development of a quick, safe and effective hemostatic material are imperative.
The main components of the current hemostatic materials for clinical and market applications, such as gauze, sponge, bandage, gel, spray and dressing, are derived from natural polymers (chitosan, gelatin, collagen, cellulose and seaweed salt), synthetic polymers (such as polycyanoacrylate, polyacrylic acid and polylactic acid) or inorganic species (such as kaolin and zeolite), but the hemostatic materials have the problems of poor hemostatic effect, potential toxicity, inconvenient storage, no degradation, poor hemostatic effect on different types or irregular wounds and the like. Particularly, the absorbable hemostatic material has important significance for wound emergency treatment and rapid hemostasis, has the characteristics of small tissue damage, simple and convenient operation, rapid hemostasis and the like due to the fact that the absorbable hemostatic material can be absorbed in vivo without being taken out, but the absorbable hemostatic material in the prior art still has certain cytotoxicity, is easy to adhere to blood scabs due to partial degradation materials, and is easy to cause bleeding in the taking-out process.
Therefore, the preparation of the degradable hemostatic material which is safe, efficient, economical, portable and adjustable in characteristics has important clinical significance. An ideal hemostatic material should meet the following requirements: (1) the hemostasis is rapid, and the hemostasis can be realized within 2min when the bleeding amount is large; (2) the individual selection can be carried out according to different types of bleeding wounds; (3) the use is simple, and even untrained people or wounded persons can use the training device by themselves; (4) light weight and durable performance; (5) degradable and no pollution. However, there is currently no hemostatic material that can simultaneously meet the above requirements. Therefore, the development of more effective and economical hemostatic materials is a technical problem to be solved.
Disclosure of Invention
In view of the above, the technical problem to be solved by the present invention is to provide a polylactic acid based polyester hemostatic sponge, and a preparation method and an application thereof, wherein the prepared hemostatic sponge has high biocompatibility and degradability, a large absorption amount, and a good blood coagulation effect.
The invention provides a polylactic acid-based polyester hemostatic sponge which is prepared by mixing PLGA and PLCL.
The PLGA includes one or both of unmodified PLGA and end-modified PLGA.
The end group modified PLGA is PLGA modified by one or more of amino, aldehyde and carboxyl.
Preferably, in the PLGA, the molar ratio of the monomers LA and GA is 0:10 to 10:0, preferably, the molar ratio of LA to GA is not 0, more preferably, the molar ratio is 1:9 to 9:1, and even more preferably, 3:7 to 7: 3.
Preferably, in the PLCL, the molar ratio of the monomers CL to LA is 0: 10-10: 0, preferably, the molar ratio of CL to LA is not 0, more preferably, the molar ratio is 1: 9-9: 1, and even more preferably, the molar ratio is 4: 6-6: 4.
Preferably, the molecular weight of the PLGA is 500-100000 Da, and more preferably 5000-50000 Da.
Preferably, the molecular weight of the PLCL is 500-100000 Da, and more preferably 5000-50000 Da.
Preferably, the molar ratio of the PLGA to the PLCL is 0: 10-10: 0, preferably, the molar ratio of the PLGA to the PLCL is not 0, more preferably 1: 9-9: 1, and even more preferably 1: 2-2: 1.
The hemostatic material provided by the invention is spongy, can block the invasion of bacteria and control the permeability of water vapor, and the porous structure of the hemostatic material is beneficial to the discharge of secretion of wounds and the promotion of tissue healing.
The invention provides a preparation method of polylactic acid based polyester hemostatic sponge, which comprises the following steps:
s1) dissolving a polyester compound into an organic solvent to obtain a polyester solution;
the polyester compound comprises PLGA and PLCL; the PLGA comprises one or two of unmodified PLGA and end group modified PLGA;
the end group modified PLGA is PLGA modified by one or more of amino, aldehyde and carboxyl;
s2) freeze-drying the polyester solution to obtain the polylactic acid based polyester hemostatic sponge.
The molar ratio of the monomers LA and GA in the PLGA and the molar ratio of the monomers LA and CL in the PLCL are the same as above, and are not described herein again. In the polyester solution, the total concentration of PLGA and PLCL is preferably 1 wt% to 20 wt%.
According to the invention, the organic solvent is preferably an organic solvent with a freezing point of-20 ℃. Further preferred is dimethyl sulfoxide (DMSO).
According to the invention, the polyester solution also comprises auxiliary additives.
The auxiliary additive is preferably any one or mixture of gelatin, thrombin, antibacterial agent, Yunnan white drug powder, Notoginseng radix, herba Cephalanoploris, rhizoma Bletillae, and pollen Typhae.
Preferably, after the auxiliary additive is added, the system is continuously stirred for 1-3 hours at the temperature of 20-60 ℃ to prepare a mixed solution.
The invention provides application of the polylactic acid-based polyester hemostatic sponge as a hemostatic dressing.
Compared with the prior art, the invention provides the polylactic acid-based polyester hemostatic sponge which is prepared by mixing PLGA and PLCL. The invention can adjust the properties of the polylactic acid based polyester hemostatic sponge such as aperture, water absorption characteristic, hemostatic ability, mechanical property, skin adhesion ability and the like to treat hemostasis of various wound surfaces by changing the proportion of monomers LA and GA in PLGA and the proportion of CL and LA in PLCL.
Drawings
FIG. 1 is a scanning electron microscope image of polylactic acid based polyester hemostatic sponge prepared from a 5% polyester solution as in example 1;
FIG. 2 is a scanning electron microscope image of a polylactic acid based polyester hemostatic sponge prepared from a 25% polyester solution of example 1;
fig. 3 is a scanning electron microscope image of the coagulation enhancement type polylactic acid based polyester hemostatic sponge prepared in example 2.
Detailed Description
In order to further illustrate the present invention, the following will describe in detail the polylactic acid based polyester hemostatic sponge, its preparation method and application in conjunction with the examples.
Example 1
(1) Synthesis of polylactide-glycolide copolymers (PLGA):
weighing certain amounts of LA and GA with a molar ratio of 5:5, placing the LA and GA into a 250mL three-neck flask, placing the three-neck flask containing the medicines into an oil bath pan, connecting a condensing device, checking the airtightness of a reaction system, vacuumizing the system, and filling nitrogen back into the system. The reaction was then evacuated and aerated, the aeration flow rate was kept at 10mL/min after 4 repetitions, the magnetic stirrer was turned on and the temperature was raised to 155 ℃ for 2 h. Slowly reducing the system pressure to 0.01MPa, and reacting for 3 h; then reacting for 4 hours under 0.001 MPa; finally, the temperature is increased to the polymerization temperature (Tp) within the range of 160-175 ℃ for continuous reaction for 60 hours.
(2) The preparation method of the amino-terminated PLGA polymer comprises the following steps:
mixing the PLGA copolymer, 4- (dimethylamino) pyridine, succinic anhydride and dichloromethane according to the mass ratio of 5:1:1:50, fully dissolving, and stirring for 4 hours; distilling under reduced pressure to remove most of dichloromethane concentrated solution; the remaining mixture was precipitated 3 times in methanol, the solid was separated and dried under vacuum to obtain end-carboxylated PLGA polymer. I.e., PLGA-COOH. Dissolving PLGA containing terminal carboxyl in anhydrous dichloromethane, adding N, N' -Carbonyl Diimidazole (CDI) into the solution, activating carboxyl for 0.5h, adding hexamethylene diamine into the solution, reacting for 8, precipitating the product with ethanol, washing and drying to obtain PLGA-NH 2 。
(3) Synthesis of polylactide-caprolactone copolymer (PLCL):
adding LA and CL in a certain mass ratio (5:5) into a reaction bottle, mixing uniformly, slowly heating to 140 ℃ under the condition of 70Pa, performing prepolymerization for 3h, filling pure nitrogen into the bottle for protection after finishing prepolymerization, and adding 0.5% of catalyst SnCl 2 Vacuumizing, reacting for 12h under the absolute pressure of 70Pa, stopping heating, cooling to 50 ℃, removing vacuum, purifying the obtained product by using chloroform as a dissolving agent and a methanol solution as a precipitating agent, and drying the purified product in vacuum at 50 ℃ for later use.
(4) Preparation of polylactic acid-based polyester solution
PLGA and PLCL (mass ratio 1:1) are prepared into polyester solutions with mass fractions of 5% and 25%, gelatin is prepared into gelatin solution with mass fraction of 15%, then the polyester solution and the gelatin solution are mixed respectively and stirred for reaction for 3 hours at 45 ℃ to prepare 2 kinds of compound liquid. Wherein the solvent is dimethyl sulfoxide.
(5) Respectively pouring the composite solutions into a mold, freezing at-20 deg.C for 3 hr, and freeze-drying in a freeze-drying machine to obtain two kinds of polylactic acid based polyester hemostatic sponges with different pore diameters (fig. 1 and fig. 2).
Example 2
(1) Preparing a composite solution with the polyester mass fraction of 5% according to the method of example 1;
(2) adding adjuvant additive Yunnan white drug powder into the above complex liquid to a final concentration of 1mg/ml, and stirring at 25 deg.C for 1 hr to obtain mixed solution.
(3) Pouring the mixed solution into a mold, freezing at-20 deg.C for 3 hr, and freeze-drying in a freeze-drying machine to obtain the coagulation-enhanced polyester hemostatic sponge (fig. 3).
Example 3 hemostatic sponge characterization
Different mass fractions of polyester hemostatic sponges prepared in example 1 were photographed by scanning electron microscopy, as shown in fig. 1.
As can be seen from FIG. 1, the pore size of the hemostatic sponge with 5% polyester content is mainly distributed in the range of 5-10 μm; as can be seen from FIG. 2, the pore size of the hemostatic sponge with 25% polyester content is mainly distributed in the range of 2-5 μm. As can be seen from figure 3, the addition of Yunnan white drug powder has little influence on the aperture.
And (3) testing water absorption rate:
the 3 hemostatic sponges prepared in examples 1 and 2 were each cut into cubes of 0.5cm x 0.5cm and weighed as M 0 It was placed in a clean, dry petri dish, the total weight being weighed to M 1 Dropping proper amount of deionized water, sucking excessive water after the sponge absorbs water sufficiently, and weighing as M 2 The water absorption capacity a is calculated by the following formula:
A＝(M 2 –M 1 )/M 0
the water absorption capacity of the test is shown in Table 1.
TABLE 1 absorption Capacity of different polylactic acid polyester sponges
Blood coagulation index test:
the 3 hemostatic seas prepared in examples 1 and 2Cutting cotton into cubes of 1cm gamma 1cm, placing into a clean beaker, water-bathing at 37 deg.C for 0.5 hr, adding 50 μ L fresh anticoagulated rabbit blood, adding 40 μ L0.2 mol/L CaCl 2 The solution was incubated for 5min, 50mL of deionized water was added, the mixture was shaken at 37 ℃ and 70rpm for 5min, the supernatant was taken to determine the absorbance value (Ab) at 540nm, and the blood coagulation index BCI was calculated by the following formula, using a physiological saline solution as a control:
BCI＝Ab sample (I) /Ab Control of ×100％
The BCI was tested as shown in Table 2.
TABLE 2 different polylactic acid polyester sponges BCI (%)
Testing a hemostasis test:
the method comprises the steps of taking a healthy rat, exposing the liver after opening the abdomen after anesthesia, cutting 3mm liver tissue at the left lobe of the liver by ophthalmic scissors to form an open bleeding wound model, sealing a wound by using a corresponding polylactic acid-based polyester hemostatic sponge after 5 seconds of free bleeding, pressing for 20 seconds by using a 10g weight, taking down and observing for 30 seconds, and recording the hemostatic time. Intraoperatively, the blood was collected using weighed sterile gauze and weighed.
The hemostasis time and the amount of bleeding were measured and calculated as shown in tables 3 and 4, respectively.
TABLE 3 hemostasis time (seconds) for different polylactic acid polyester sponges treated wounds
TABLE 4 bleeding volume (g) of different polylactic acid polyester sponges treated wounds
The above description of the embodiments is only intended to facilitate the understanding of the method of the invention and its core idea. It should be noted that, for those skilled in the art, it is possible to make various improvements and modifications to the present invention without departing from the principle of the present invention, and those improvements and modifications also fall within the scope of the claims of the present invention.
Claims (10)
1. The polylactic acid-based polyester hemostatic sponge is characterized by being prepared by mixing PLGA and PLCL;
the PLGA comprises one or two of unmodified PLGA and end group modified PLGA;
the end group modified PLGA is PLGA modified by one or more of amino, aldehyde and carboxyl.
2. The polylactic acid-based polyester hemostatic sponge according to claim 1, wherein in the PLGA, the molar ratio of the monomers LA and GA is 0: 10-10: 0;
in the PLCL, the molar ratio of the monomers LA and CL is 0: 10-10: 0.
3. The polylactic acid based polyester hemostatic sponge according to claim 1, wherein the molecular weight of the PLGA is 500-100000 Da;
the molecular weight of the PLCL is 500-100000 Da.
4. The polylactic acid-based polyester hemostatic sponge according to claim 1, wherein the molar ratio of PLGA to PLCL is 0:10 to 10: 0.
5. A preparation method of polylactic acid based polyester hemostatic sponge comprises the following steps:
s1) dissolving a polyester compound into an organic solvent to obtain a polyester solution;
the polyester compound comprises PLGA and PLCL; the PLGA comprises one or two of unmodified PLGA and end-modified PLGA;
the end group modified PLGA is PLGA modified by one or more of amino, aldehyde and carboxyl;
s2) freeze-drying the polyester solution to obtain the polylactic acid based polyester hemostatic sponge.
6. The method according to claim 5, wherein the PLGA has a molar ratio of the monomers LA and GA of 0:10 to 10: 0;
in the PLCL, the molar ratio of the monomer LA to the monomer CL is 0: 10-10: 0.
7. The method of claim 5, wherein the total concentration of PLGA and PLCL in the polyester solution is 1 to 20 wt.%.
8. The preparation method according to claim 5, wherein the organic solvent is an organic solvent having a freezing point of-20 to 20 ℃.
9. The method according to claim 5, wherein the polyester solution further comprises an auxiliary additive;
the auxiliary additive is one or more of gelatin, thrombin, antibacterial agent, Yunnan white drug powder, Notoginseng radix, herba Cephalanoploris, rhizoma Bletillae, and pollen Typhae.
10. Use of a polylactic acid based polyester haemostatic sponge according to any of claims 1 to 4 as a haemostatic dressing.
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| CN202210899664.0A CN115089759A (en) | 2022-07-28 | 2022-07-28 | Polylactic acid-based polyester hemostatic sponge and preparation method and application thereof |
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| CN202210899664.0A CN115089759A (en) | 2022-07-28 | 2022-07-28 | Polylactic acid-based polyester hemostatic sponge and preparation method and application thereof |
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| US20040175408A1 (en) * | 2003-03-07 | 2004-09-09 | Iksoo Chun | Method of preparation of bioabsorbable porous reinforced tissue implants and implants thereof |
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| CN102247615A (en) * | 2011-06-25 | 2011-11-23 | 四川大学 | Gelatine-PCL (posterior cruciate ligament) dental hemostatic sponge and preparation method thereof |
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| US20170246339A1 (en) * | 2011-09-26 | 2017-08-31 | Yes, Inc. | Novel hemostatic compositions and dressings for bleeding |
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| US20180250231A1 (en) * | 2015-09-11 | 2018-09-06 | Ewha University - Industry Collaboration Foudation | Polymeric microspheres with spontaneous pore-closing functionality and methods for preparign the same |
| CN114634634A (en) * | 2022-03-22 | 2022-06-17 | 陈凌卉 | Biological function composite porous polyester microsphere and preparation method thereof |
-
2022
- 2022-07-28 CN CN202210899664.0A patent/CN115089759A/en active Pending
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20040175408A1 (en) * | 2003-03-07 | 2004-09-09 | Iksoo Chun | Method of preparation of bioabsorbable porous reinforced tissue implants and implants thereof |
| CN1727013A (en) * | 2005-06-10 | 2006-02-01 | 惠州华阳医疗器械有限公司 | Hemostatic material in medical use |
| CN102247615A (en) * | 2011-06-25 | 2011-11-23 | 四川大学 | Gelatine-PCL (posterior cruciate ligament) dental hemostatic sponge and preparation method thereof |
| US20170246339A1 (en) * | 2011-09-26 | 2017-08-31 | Yes, Inc. | Novel hemostatic compositions and dressings for bleeding |
| CN107106496A (en) * | 2014-12-30 | 2017-08-29 | 株式会社三养生物制药 | High molecular nanometer particles freeze-drying thing and preparation method thereof |
| US20180250231A1 (en) * | 2015-09-11 | 2018-09-06 | Ewha University - Industry Collaboration Foudation | Polymeric microspheres with spontaneous pore-closing functionality and methods for preparign the same |
| CN107469132A (en) * | 2017-07-26 | 2017-12-15 | 中国科学院长春应用化学研究所 | A kind of styptic sponge/medicine-loading fibre felt/styptic sponge compound and preparation method thereof |
| CN114634634A (en) * | 2022-03-22 | 2022-06-17 | 陈凌卉 | Biological function composite porous polyester microsphere and preparation method thereof |
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