KR102208921B1 - Shape memory polymer, preparation method thereof, and the use of the same - Google Patents

Abstract

The present invention has shape memory properties, biodegradability, and biocompatibility at the same time, and can be applied to medical materials such as stents, tissue adhesives, tissue sealants, hemostatic agents, anti-adhesion agents, or tissue engineering scaffolds. The manufacturing method and use are disclosed.

Description

Shape memory polymer, preparation method thereof, and the use of the same}

The present invention relates to a shape memory polymer, a method of manufacturing the same, and a use thereof.

Recently, research on tissue engineering to develop artificial organs that can replace the roles of organs that have been ill and have been removed due to cessation of function has been in the spotlight. Biotransplantation materials, which are mainly manufactured through biomaterials, are being studied in the direction of regenerating or replacing damaged tissues, organs, and organs, and attention is focused on this.

In the past, silicon or metal was used, but these materials were permanently present in the human body even after their role was ended, causing inflammation and other diseases. In order to overcome this, biodegradable polymers that undergo decomposition in the human body are currently being used.

Biodegradable polymers are divided into natural polymers and synthetic polymers, of which synthetic polymers are being studied due to the advantage of being able to control physical properties, biocompatibility, and biodegradability.

In 2002, the Langer team of the United States developed a new biodegradable polyester polymer PGS [Y. Wang, GA Ameer, BJ Sheppard and R. Langer, “A Tough Biodegradable Elastomer,” Nature Biotechnology , Vol. 20, No. 6, 2002, pp. 602-606]. Compared to other polyester polymers, it has high elasticity and has a low biodegradation period, so many studies are being conducted in the field of application that can use it. At this time, Langer's research team developed poly(glycerol-sebacic acid), a polyester elastomer that is biodegradable and biocompatible. The poly(glycerol-sebacic acid) showed good biocompatibility in vitro and in vivo , and a study result showing a biodegradation period of 2 months in animal experiments. Through this, many researchers have studied to apply new polyester.

In 2008, Young-Ha Lee and three others disclosed the contents of a poly(3-hydroxyalkanoate) block copolymer having shape memory capability in Korean Patent Publication No. 10-2008-0032029. In this patent, it is stated that when a PHA block copolymer is made by selectively adjusting the ratio of monomers, it has elasticity and temperature-sensitive shape memory ability, and can be used as medical materials, household goods materials, and industrial materials. However, as a result of the shape memory property test, the copolymer disclosed in the above patent has a disadvantage that it is difficult to have shape memory properties in the body because the shrinkage proceeds at 45°C or higher.

Meanwhile, in Korean Patent Laid-Open No. 10-2016-0044339, Chan-hee Jeong and two others used biodegradable polymers with shape memory properties to reduce the inflammatory side effects of the Maeseon Rope method, a skin treatment method used for cosmetic and medical purposes. The method for manufacturing the used Maeseon Rope was disclosed. If this method is used, the skin is pulled using the shape-memory ability of the ropes remaining in the body, and the ropes are melted within a few months and absorbed into the body, thereby eliminating the need for secondary removal. However, there is a disadvantage in that only the contents of the manufacturing method are described in the registered patent, and there is no actual result of the experiment.

In addition, in Korean Patent Publication No. 10-2016-0069499, Kim Hyung-il et al. disclosed a method of manufacturing a biodegradable stent having shape memory capability. According to this manufacturing method, a desired stent was manufactured using several biodegradable polymers, and the shape memory result was shown. However, since the result of the shape memory ability was shown at a temperature higher than the body temperature, it is somewhat difficult to show the shape memory ability inside the body.

In addition, in 2016, Mohanty's research team polymerized glycerol, sebacic acid, and stearic acid to prepare a copolymer as follows [AK Mohanty, M. Misra and G. Hinrichsen, “Biofibres, Biodegradable Polymers and Biocomposites: An Overview, M acromolecular Materials and Engineering , Vol. 276-277, No. 1, 2000, pp. 1-24].

In this document, it was confirmed that the crosslinked polymer exhibited shape memory characteristics through various ratios. However, when crosslinking is performed, it has a disadvantage that crosslinking proceeds under difficult conditions, and has a disadvantage of having a low shape restoration rate of 85%.

Korean Patent Publication No. 10-2008-0032029 (2008.04.14), Poly(3-hydroxyalkanoate) block copolymer with shape memory function Korean Patent Laid-Open No. 10-2016-0044339 (2016.04.25), A method for manufacturing a medical rodent rope using a shape-memory bioabsorbable polymer material, and a manufacturing apparatus and product thereof Korean Patent Publication No. 10-2016-0069499 (2016.06.16), Biodegradable stent and its shape memory expansion method

Y. Wang, G. A. Ameer, B. J. Sheppard and R. Langer, “A Tough Biodegradable Elastomer,” Nature Biotechnology, Vol. 20, No. 6, 2002, pp. 602-606 A. K. Mohanty, M. Misra and G. Hinrichsen, “Biofibres, Biodegradable Polymers and Biocomposites: An Overview,” Macromolecular Materials and Engineering, Vol. 276-277, No. 1, 2000, pp. 1-24.

Accordingly, the present inventors continued research on the poly(glycerol-sebacate) polymer, and prepared a shape memory polymer with a novel structure by adding a higher fatty acid capable of reacting with OH of glycerol during the production of the polymer. It was confirmed that the memory polymer can be deformed by temperature, and the deformation can be controlled by setting an arbitrary shape restoration temperature.

Accordingly, an object of the present invention is to provide a shape memory polymer having a new structure and a method for manufacturing the same.

Another object of the present invention is to provide the use of the shape memory polymer.

In order to achieve the above object, the present invention provides a shape memory polymer comprising a repeating unit represented by the following formula (1):

[Formula 1]

(In Formula 1, R ₁ , R ₂ , R ₃ and n are as described in the specification.)

In addition, the present invention, as shown in the following scheme 1,

(a) reacting the compound of formula 3 and the compound of formula 4; And

(b) reacting the obtained polymer of Chemical Formula 5 with the compound of Chemical Formula 6; it provides a method for preparing a shape memory polymer represented by Chemical Formula 1.

[Scheme 1]

(In Reaction Scheme 1, R ₁ , R ₂ and n are as described in the specification.)

In addition, the present invention provides the use of the shape memory polymer as a medical material.

The shape memory polymer according to the present invention has shape memory properties, biodegradability, and biocompatibility at the same time, and can be applied in various fields not only to medical materials but also to electronics, automobiles, food, cosmetics, and agriculture.

1 is a ¹ H-NMR spectrum of the PGSS-S copolymer prepared in Example 1.
2 is a photograph showing the curing of the PGSS-S film.
3 is a crosslinked PGSS-S film and DSC analysis results of the PGS film.
4 is a photograph showing the shape memory characteristics of Sample C, Sample D, and Sample E.

In the present invention, a shape memory polymer having a new structure, a manufacturing method and use thereof are proposed.

Specifically, the shape memory polymer is represented by the following formula (1).

[Formula 1]

(In Formula 1,

R ₁ is a linear or branched C6 to C25 alkyl group, and is a linear or branched C6 to C25 hydroxy alkyl group,

R ₂ is HOC(=O)(CH ₂ ) ₈ -C(=O)O-, CH ₃ (CH ₂ )rCOO-(6≤r≤25), or -[A]a-[B]b- [C]c, wherein A is -OC(=O)(CH ₂ ) ₈ -C(=O)O- or HOC(=O)(CH ₂ ) ₈ -C(=O)O-, and B Is -CH ₂ -CH(OH)CH ₂ -or HOCH ₂ -CH(OH)CH ₂ -, and C is -(CH ₂ )rCOO- or CH ₃ (CH ₂ )rCOO-(8≤r≤20) And, 1≤a≤10, 1≤b≤10, and 0≤c≤10,

n is an integer from 1 to 100.)

In Formula 1, R ₁ is a functional group derived from a higher fatty acid, and is a linear or branched C6 to C25 alkyl group, and is selected from a linear or branched C6 to C25 hydroxyalkyl group. It is preferably a linear or branched C8 to C20 alkyl group, and a linear or branched C8 to C20 hydroxyalkyl group. More preferably, R ₁ is a caprylic group, a patr group, an undecanyl group, a lauryl group, a tridecanyl group, a myristyl group, a pentadecanyl group, a palmit group, a palmitoreyl group, a heptadecanyl group, a stearyl group, an ole Diary, ricinolenyl group, linoleyl group, arachidyl group, arachidonyl group, tricosanoyl group, erucyl group, behenyl group, lignoceryl group, or nerbonyl group, most preferably stearyl group. At this time, in the hydroxy alkyl group, 1 to 6 hydroxy groups may be substituted.

R ₂ has OH and CO ₂ H groups, which are functional groups capable of crosslinking by heat, and may be one or more selected from the group consisting of glycerol, sebacic acid and higher fatty acids.

Specifically, HOC(=O)(CH ₂ ) ₈ -C(=O)O- derived from sebacic acid or CH ₃ (CH ₂ )rCOO-(8≦r≦ ₂₀ ) derived from a higher fatty acid, or glycerol , It may be -[A]a-[B]b-[C]c including sebacic acid and higher fatty acids. At this time, A is -OC(=O)(CH ₂ ) ₈ -C(=O)O- or HOC(=O)(CH ₂ ) ₈ -C(=O)O-, and B is -CH ₂ -CH (OH)CH ₂ -or HOCH ₂ -CH(OH)CH ₂ -, C is -(CH ₂ )rCOO- or CH ₃ (CH ₂ )rCOO-(8≤r≤20), and 1≤a≤ 10, 1≤b≤10, and 0≤c≤10, specifically 1≤a≤5, 1≤b≤5, and 0≤c≤5.

At this time, -[A]a-[B]b-[C]c means a randomly connected structure. For example, -[A]a-[B]b-[C]c is randomly connected such as -AB, -ABC, -ABA, -ABAB, -ABABA, -ABABC, -ABABAB, -ABABABA, -ABABABC, etc. It can have a structure. At this time, when A is located at the end, A is in the form of HOC(=O)(CH ₂ ) ₈ -C(=O)O-, and when B is located at the end, B is HOCH ₂ -CH(OH)CH ₂ In the form of O-, when C is located at the terminal, C may be in the form of CH ₃ (CH ₂ )rCOO-.

Preferably, the shape memory polymer of Formula 1 is represented by the following Formula 2, and poly(glycerol-co-sebacate-stearate) (PGSS, poly(glycerol-) having a reactive group (R ₂ ) in the side chain and the terminal co-sebacate)-stearate).

[Formula 2]

(In Chemical Formula 2, R ₂ and n are as described above.)

More specifically, the shape memory polymer of Formula 1 may be any one of Formulas 2a to 2d.

[Formula 2a]

[Formula 2b]

[Formula 2c]

[Formula 2d]

The shape memory polymer according to the present invention may have a weight average molecular weight of 500 to 5,000 g/mol, 600 to 4,500 g/mol, 700 to 4,000 g/mol, 1000 to 4,000 g/mol, and 2000 to 4,000 g/mol.

The shape memory polymer may have an elongation of 40% or more after heat curing, specifically 80% or more, and more specifically 140 to 200%. In addition, the shape memory polymer may have a strain recovery rate of 80 to 100% after heat curing, and specifically 87 to 99%. The improvement of the elongation rate and the deformation recovery rate of the shape memory polymer may be a result of an increase in the weight average molecular weight of the shape memory polymer.

The shape memory polymer according to the present invention includes the steps of: (a) reacting the compound of Formula 3 and the compound of Formula 4 as shown in Scheme 1 below; And (b) reacting the obtained polymer of formula 5 with a compound of formula 6;

[Scheme 1]

(In Reaction Scheme 1, R ₁ and R ₂ , and n are as described in the specification.)

It will be described in detail for each step below.

First, a polymer of Formula 5 is prepared through an esterification reaction of sebacic acid represented by Formula 4 using glycerol, a compound represented by Formula 3 as an initiator.

[Formula 3]

[Formula 4]

[Formula 5]

Glycerol of formula 3 and sebacic acid of formula 4 are in a molar ratio of 1:0.1 to 1:10, a molar ratio of 1:0.5 to 1:5, a molar ratio of 1:0.7 to 1:3, preferably a molar ratio of 1:1 Perform.

The reaction is usually carried out at 50 to 180°C, 80 to 170°C, 90 to 160°C, preferably 140 to 150°C.

At this time, the reaction time may be 1 to 72 hours, 5 to 60 hours, 10 to 40 hours, 15 to 30 hours, preferably 18 to 25 hours so that the esterification reaction can sufficiently occur.

This reaction is carried out in an atmosphere of an inert gas (eg, nitrogen, argon).

In order to increase the reaction rate by moving the chemical equilibrium in the esterification reaction, water and/or an unreacted diol compound may be discharged out of the reaction system by evaporation or distillation.

This reaction uses a solvent if necessary.

The solvent is not particularly limited as long as it does not adversely affect the reaction, and examples thereof include water; Alcohols such as methanol, ethanol, 2-propanol, and 2-methyl-2-propanol; Aromatic hydrocarbons such as benzene, toluene and xylene; Amides such as N,N-dimethylformamide, N,N-dimethylacetamide and 1-methyl-2-pyrrolidone; Halogenated hydrocarbons such as methylene chloride, chloroform and dichloroethane; Ethers such as dioxane, tetrahydrofuran, anisole, ethylene glycol dimethyl ether, diethylene glycol dimethyl ether, and diethylene glycol diethyl ether; Ketones such as acetone and 2-butanone; Nitriles such as acetonitrile; Esters such as ethyl acetate and butyl acetate, and sulfoxides such as dimethyl sulfoxide, and the like, and they may be mixed and used.

This reaction uses a catalyst if necessary.

Calcium acetate, manganese acetate, magnesium acetate, zinc acetate, monobutyl tin oxide, dibutyl tin oxide, dibutyltin dichloride, monobutylhydroxy tin oxide, octyltin, tetra Butyl tin, tetraphenyl tin, triethyl titanate, acetyltripropyl titanate, tetramethyl titanate, tetrapropyl titanate, tetraisopropyl titanate, tetra n-butyl titanate and tetra(2-ethylhexyl) titanate It may contain at least one metal compound selected from the group consisting of

If necessary, the polymer of Formula 5 obtained after the reaction with the ester can be applied to the next step by performing a separate purification process. At this time, the purification process is not particularly limited in the present invention, and a process using known dialysis, filtration, electrophoresis or chromatography may be used.

Next, the polymer of Formula 5 is reacted with the compound of Formula 6 to prepare a polymer of Formula 1.

[Formula 6]

[Formula 1]

(In Formulas 1 and 6, R ₁ and n are as mentioned above.)

The polymer of Formula 1 has a structure in which a higher fatty acid (derived from Formula 6, R ₁ COO-) is present at the end group or at the R ₂ position.

The higher fatty acid, which is a compound of Formula 6, is a linear or branched C6~C25 alkyl group, and a compound containing a linear or branched C6~C25 hydroxyalkyl group may be used. Specifically, usable higher fatty acids include Caprylic acid, Capric acid, Undecanoic acid, Lauric acid, Tridecanoic acid, and Myristic acid. (Myristic acid), Pentadecanoic acid, Palmitic acid, Palmitoleic acid, Heptadecanoic acid, Stearic acid, Oleic acid, Rishi Noleic acid, Linoleic acid, Arachidic acid, Arachidonic acid, Tricosanoic acid, Erucic acid, Behenic acid ( Behenic acid), lignoceric acid, and at least one selected from the group consisting of nervonic acid may be used, and stearic acid is preferably used.

In this reaction, the polymer of Formula 5 and the higher fatty acid of Formula 6 are in a molar ratio of 1:0.1 to 1:5, a molar ratio of 1:0.5 to 1:4, a molar ratio of 1:0.5 to 1:3, preferably 1:2 It is carried out in a molar ratio of

The reaction varies depending on the type of higher fatty acid to be used, and is usually carried out at 50 to 180°C, 80 to 170°C, 90 to 160°C, and preferably 140 to 150°C.

At this time, the reaction time is carried out within a time that the polymer of Formula 5 and the higher fatty acid of Formula 6 can sufficiently react, and 1 to 72 hours, 5 to 60 hours, 10 to 40 hours, 15 to 30 hours, preferably 18 To 25 hours.

If necessary, the reaction is carried out under reduced pressure to remove water generated during the reaction, and at this time, it may be carried out by adjusting the pressure of 1 torr to 40 mtorr.

This reaction can be carried out in an atmosphere of an inert gas (eg, nitrogen, argon), and if necessary, can be carried out in the presence of a solvent and a catalyst. Details follow the above-mentioned.

Specifically, in Formula 1, R ₂ may be any one substituent selected from the group consisting of Formula 3, Formula 4, Formula 6, and polymers thereof.

According to one embodiment, R ₂ may be a substituent derived from sebacic acid represented by Chemical Formula 4, and in this case, it is possible to prepare a shape memory polymer represented by Chemical Formula 2a.

According to another embodiment, R ₂ may be a substituent derived from a higher fatty acid represented by Chemical Formula 6, and in this case, it is possible to prepare a shape memory polymer represented by Chemical Formula 2b.

According to another embodiment, R ₂ may be a substituent derived from a polymer obtained by reacting a compound of Formula 3, Formula 4, and Formula 6 together, in which case the preparation of a shape memory polymer represented by Formula 2c or Formula 2d Is possible.

The shape memory polymer of Formula 1 according to the present invention prepared through the above steps can be molded into various forms through curing, and the molded article obtained at this time has shape memory properties, biodegradability, and biocompatibility at the same time.

The curing may be a thermosetting method.

Thermal curing is to form a cross-linked (or network) structure by applying heat, and hydrogen bonds between the carboxyl group and the hydroxy group present in the structure of Formula 1 occur in various ways to form the cross-linked structure. To form.

The thermosetting process may vary depending on the molecular weight of the shape memory polymer of Formula 1 and the composition of the repeating unit, but at 60 to 160°C, preferably at 70 to 160°C, more preferably at 75 to 140°C, for 5 hours to 72 hours , By performing for 10 to 48 hours.

The thermosetting shape memory polymer has a degree of crosslinking of 20% to 97%. The degree of crosslinking can be achieved by controlling the crosslinking time, temperature, or concentration, and can be applied to various fields due to the easy control of the degree of crosslinking.

If necessary for thermal curing, a thermal initiator may be further included.

At this time, the shape memory polymer of Formula 1 may be applied in the form of a coating film by forming a coating layer on a substrate, or may be processed into various types of molded products. At this time, the molded product may be processed into various forms, such as a film, sheet, container, net, laminate, and 3D molded product.

The coating method is not particularly limited, but known methods such as spray coating, spin coating, dip coating, bar coating, and gravure coating are used.

In addition, the molding process during molding is not particularly limited in the present invention, and injection molding, extrusion molding, compression molding, transfer molding, thermoforming, flow molding, extrusion foam molding, extrusion coating, blow molding, calender molding or Lamination molding and the like are possible.

For example, the shape memory polymer of Formula 1 according to the present invention is processed in the form of a coating layer or a film, and the shape memory polymer cured through thermal curing has shape memory capability, biodegradability and biocompatibility characteristics.

Polymers with shape memory ability are called shape memory polymers (SMPs). Shape memory ability is the ability to fix it in a certain shape by applying external physical force (stress) under certain conditions (temperature, light, pH, humidity, etc.), and to restore it to its original state when the external physical force is removed. Means.

In shape memory materials, the transition temperature that exhibits formation memory properties generally has elasticity like rubber at a temperature higher than the glass transition temperature (Tg) or melting temperature (Tm). It is important to know the transition temperature range that exerts.

Accordingly, the crosslinked shape memory polymer according to the present invention has both a glass transition temperature (Tg) and a melting temperature (Tm) as a phase transition temperature when the storage modulus according to temperature change is measured, and the melting temperature ( Tm) or more, the storage modulus is maintained at a constant value.

Specifically, the method of using the crosslinked shape memory polymer is to first deform the shape memory polymer by an external force at a melting temperature (Tm) or higher, then cool to a glass transition temperature (Tg), and the first transformation. When removing the force that caused it, the first deformed shape is maintained. At this time, the restoration may be performed by heating above the melting temperature (Tm).

If necessary, apply additional force at the glass transition temperature (Tg) to perform secondary deformation, cool to room temperature, and then remove the force that caused the secondary deformation to maintain the secondary deformed shape. It can be restored by heating the temperature to the temperature (Tg).

According to an embodiment, the crosslinked shape memory polymer of the present invention is 7 to 40°C, preferably a melting temperature (Tm) of 20°C to 40°C similar to the biological temperature, and -40 to -25°C. It has a glass transition temperature (Tg). When the melting point of the crosslinked shape memory polymer is less than the above range, the shape of the material is deformed at room temperature, so there is a limit to its application as a physiology application device. Conversely, when it exceeds the above range, the deformation recovery rate decreases and the shape of the material Problems with poor memory skills can occur.

In particular, the shape memory polymer crosslinked after heat curing according to an embodiment of the present invention is 70% or more, preferably 70% to 100% of the strain recovery rate at 7 to 40°C, including the temperature of the body temperature, preferably Since it exhibits a strain recovery rate of 80% to 100%, more preferably 87% to 99% at a temperature of 20 to 40°C, various applications can be applied to physiological medical applications or medical materials.

On the other hand, the shape memory polymer and the crosslinked shape memory polymer according to the present invention may be referred to as a biodegradable polymer because of its biodegradable properties that are slowly degraded in the human body.

As used herein, the term “biodegradable” means extinction after being introduced into a living body (eg, injection, insertion, or implantation) independently of the reaction before the extinction occurs such as dissolution, decomposition, absorption and excretion. Indicates that the material is selected to be The kind of such a material can be easily selected by a person of ordinary skill in the art. These substances are sometimes referred to by other terms such as “bioresorbable”, “bioabsorbable” or “biodegradable” depending on the reactor that is being destroyed. Here, the term "bio" is the opposite of other erosion processes caused by factors such as high temperature, strong acid or strong base, ultraviolet rays or climatic conditions, and indicates that erosion occurs under certain physiological conditions. .

In addition, the shape memory polymer and the crosslinked shape memory polymer according to the present invention may be referred to as a biocompatible polymer because it has a biocompatibility characteristic in which no specific reaction to a living body occurs.

The term “biocompatibility” as used herein refers to a substance that is substantially non-toxic in the body conditions formulated for the purpose of certain use and is not substantially rejected (ie, non-antigenic) by the physiological system of the patient. Show. Biocompatibility is determined by International Organization for Standardization (ISO) 10993 and/or US Pharmacopoeia (USP) 23 and/or US Food and Drug Administration (FDA) blue book memorandum G95-1 (Original title: “Use of International Standard ISO-10993, Biological Evaluation. of Medical Devices Part-1: Evaluation and Testing”). Typically, these tests measure the toxicity, infectivity, pyrogenicity, irritability, reactivity, hemolytic activity, carcinogenicity and/or immunogenicity of a substance. Biocompatible structures or substances do not cause long-lasting or synergistic harmful biological reactions when introduced into the living body of most patients, and are distinguished from mild transient inflammation usually accompanied by surgery or when foreign substances are introduced into living organisms.

Due to the characteristics of shape memory ability, biodegradability and biocompatibility as described above, the shape memory polymer of Formula 1 and crosslinked shape memory polymers thereof according to the present invention are used in the fields of electronics, automobiles, food, cosmetics, agriculture and medicine, etc. It can be widely used.

Specifically, it can be applied to medical materials.

As an application example, the medical material may be applied as an implantable medical device. The implantable medical device is a medical device that is implanted into the body, and includes intravascular stents, urinary, biliary, tracheobronchial, esophageal, and kidney for treating stenoses. It can be used as a stent for maintaining the openings of the (renal) tracts and the inferior vena cava.

Another application example may be a tissue adhesive, a tissue sealant, or a hemostatic agent.

As a tissue adhesive or tissue suture, it can replace surgical sutures, can be used to block unnecessary blood vessels, can be used for hemostasis and suture of soft tissues such as facial tissues and cartilage and hard tissues such as bones and teeth, and skin It can be used in various areas such as blood vessels, digestive organs, cranial nerves, plastic surgery, orthopedic surgery.

In addition, it may be used to adhere damaged portions of tissue, seal leaks of air/fluid from tissue, adhere medical devices to tissue, or fill defective portions of tissue. The term “living tissue” is not specifically limited, for example skin, bone, nerve, axon, cartilage, blood vessel, cornea, muscle, fascia, brain, prostate, breast, endometrial, lung, spleen, small intestine, liver, Includes testes, ovaries, neck, rectum, stomach, lymph nodes, bone marrow and kidneys.

In addition, it can be used to seal and prevent leakage of tubular structures such as blood vessels.

As another application example, it may be used as an anti-adhesion agent. Adhesion occurs at all surgical sites, and is a phenomenon in which other tissues stick around the wound around the surgical site. For example, it may be applied to exposed tissue after surgery and used to prevent adhesion between the tissue and surrounding tissue. For example, it can be used as an agent for preventing long-term adhesion, in particular as an agent for preventing intestinal adhesion.

As another application example, it can be used as a support for tissue engineering. Tissue engineering technology refers to the technology of culturing cells isolated from the patient's tissue on a scaffold to produce a cell-support complex and then transplanting it into the body.Tissue engineering technology includes artificial skin, artificial bone, artificial cartilage, artificial cornea, artificial blood vessels, It is applied to the regeneration of almost all organs of the human body such as artificial muscles. The shape memory polymer of the present invention and its crosslinked polyester can be used as a support for tissue engineering because it can be adhered to various biomolecules, and further, it can be used as a medical material such as cosmetics, wound covering materials, and dental matrices.

In addition, ophthalmic bonding such as perforation, fissure, treatment of incisions, corneal transplantation, and artificial corneal insertion; Dental bonding such as orthodontic devices, machined dentures, crown mounting, swaying teeth fixation, broken teeth treatment and filler fixation; Surgical treatments such as vascular bonding, tissue bonding, artificial material transplantation, and wound closure; Orthopedic treatments such as bone, ligament, tendon, meniscus and muscle treatment and implantation of artificial materials; Alternatively, it may be used as a carrier for drug delivery.

[Example]

Hereinafter, the present invention will be described in detail according to examples that do not limit the present invention. It goes without saying that the following examples of the present invention are intended to embodi the present invention and do not limit or limit the scope of the present invention. Therefore, what can be easily inferred by experts in the technical field to which the present invention pertains from the detailed description and examples of the present invention is interpreted as belonging to the scope of the present invention.

Example 1: Preparation of a poly(glycerol-co-sebacate-stearic acid) copolymer (PGSS-S) having a stearyl group at the terminal and side chain

Stirring was started at 150° C. to dissolve 92.7 g (0.46 mol) of sebacic acid in a 250 ml round bottom flask under a nitrogen atmosphere. After sebacic acid was dissolved, 42.2 g (0.46 mol) of glycerol was injected through a syringe, followed by stirring in this state for 23 hours.

Next, after 23 hours had passed, 65.2 g (0.23 mol) of stearic acid was injected through a paper funnel. After adding stearic acid, the mixture was stirred for about an hour, and stirring was performed under reduced pressure for 1 hour at 500 mmHg through a reduced pressure pump. After the reaction, the prepared PGSS-S copolymer was recovered.

Gel Permeation Chromatography (GPC) equipment and nuclear magnetic resonance spectroscopy (1H-NMR Spectroscopy) were used to analyze the weight average molecular weight and structure of the prepared PGSS-S copolymer.

The weight average molecular weight (MW) was measured using agilent's Gel Permeation Chromatography (GPC) equipment, and the columns used were Shodex 802, 803, 804, the solvent used was chloroform, and the flow rate was 1 mL. It was measured in /min.

Through the above reaction, the weight average molecular weight was 1,486 g/mole (Sample A), 1,756 g/mole (Sample B), 2,738 g/mole (Sample C), 3,157 g/mole (Sample D), 3,710 g/mole, respectively. (Sample E), a PGSS-S copolymer was prepared.

1 is a 1H-NMR spectrum of a PGSS-S copolymer, and it was confirmed that the PGSS-S copolymer was prepared through 1H-NMR analysis. For reference, the OH group of the glycerol (Glycerol) in FIG. 1 is substituted with any one substituent selected from the group consisting of glycerol, sebacic acid, stearic acid, and polymers thereof according to the weight average molecular weight and degree of crosslinking.

Experimental Example 1: Thermal crosslinking reaction and analysis of physical properties

(1) Preparation of crosslinked PGSS-S film

The PGSS-S copolymer prepared in Example 1 was allowed to stand at 80° C. for 30 minutes to dissolve.

Subsequently, 1 ml of a polymer was poured into a Teflon mold processed to have a width of 15 mm, a length of 50 mm, and a thickness of 0.9 mm to prepare a film using a micropipette. The mold thus prepared was put into a vacuum oven and decompressed at 120° C. and 1 torr for 48 hours. During the decompression, it was confirmed that water was generated in the polymer as the crosslinking reaction proceeded to generate air bubbles. After the crosslinking reaction was completed, it was confirmed that a transparent yellow film was formed as shown in FIG. 2.

(2) Analysis of crosslinking degree

Thermal curing was performed by varying the concentration and temperature of the PGSS-S copolymer solution in (1), and the degree of crosslinking accordingly was measured and shown in Tables 1 and 2 below. At this time, the degree of crosslinking was measured using methylene chloride capable of dissolving the PGSS-MA film with reference to KSC3004 section 28.

No Molecular weight (g/mol) Temperature(℃) Time(hr) Pressure (torr) Degree of crosslinking (%) Sample A 1,486 120 48 One 58.2 Sample B 1,756 60.1 Sample C 2,738 72.8 Sample D 3,517 68.1 Sample E 3,710 90.5

Referring to Table 1, as the molecular weight increases, the degree of crosslinking tends to increase.

In addition, referring to FIG. 2, it can be seen that the PGSS-S copolymer is present in the form of a film on the substrate and does not fall off by being attached to the bottom surface, so that thermal crosslinking occurs through heat treatment.

(3) Tm and heat of fusion measurement

The melting point and heat of fusion were measured with a sample mass of between 2 and 5 mg in an aluminum pan using a differential scanning calorimetry (DSC) equipment manufactured by TA Instrument. In addition, the speed of the ramp was measured repeatedly from -50°C to 100°C, including isothermal for 3 minutes at 10°C/min.

For comparison, conventional PGS (poly(glycerol-sebacate)) was synthesized and measured as a comparative group, and a crosslinked film was measured as an experimental group.

3 is a crosslinked PGSS-S film and DSC analysis results of the PGS film. 3, it can be seen that the crosslinked PGSS-S film according to the present invention has a Tm of 29.7°C and a PGS film of 7.5°C.

In addition, the heat of fusion (Hm; melting enthalpy) can be seen that the crosslinked PGSS-S film according to the present invention has 27.4 J/g, and the PGS film has 21.2 J/g.

Experimental Example 2: Analysis of shape memory characteristics

In order to confirm the shape memory characteristics of the crosslinked PGSS-S copolymer film (concentration 300wt/v%, 30 minutes light irradiation) according to the present invention, it was carried out as follows, and the obtained results are shown in FIG.

Experiment Early Initial film length measurement transform -Put it in 3rd distilled water at 50℃ and measure the length after stretching
-Leave for 1 minute in 3rd distilled water at 10℃ restore Length measurement after leaving for 2 minutes in 3rd distilled water at 38℃

Figure 4 is a photograph showing the shape memory characteristics of Samples C, D, and E, the crosslinked PGSS-S film according to the present invention is (a) initial state (b) deformed state (Stretched) , (c) As a result of checking the restored state (Recovery), when the temperature was adjusted back to the initial temperature, it was confirmed that the shape was restored to the initial state.

More specifically, the strain recovery rate of the crosslinked PGSS-S film was measured.

The strain recovery rate is defined by the following calculation equation 1, and can be used as an index of the shape memory behavior of the polymer resin.

[Calculation 1]

Strain recovery rate (Rr, %)={(Ie-Ir)/(Ie-Io)}×100

Io: length of initial sample

Ie: length of deformed sample

Ir: the length of the sample after recovery

Sample C Sample D Sample E Io 5.0cm 5.0cm 5.0cm Ie 9.0cm 11.9cm 7.0cm Ir 5.0cm 5.4cm 5.0cm Strain recovery rate 100.0% 91.5% 100.0%

According to Table 3, in the crosslinked PGSS-S sample C film, Io was measured as 5.0 cm, Ie was 9.0 cm, and Ir was 5.0 cm, and the elongation rate was 80.0% and the strain recovery rate was calculated to be about 100.0%, and PGSS- The S sample D film has an Io of 5.0 cm, an Ie of 11.9 cm, and an Ir of 5.4 cm, and the elongation rate is 147.9%, and the strain recovery rate is about 91.5%, and the PGSS-S sample E film has an Io of 5.0cm, Ie A was measured as 7.0cm and Ir was 5.0cm, and it was confirmed that the elongation rate was 40.0% and the strain recovery rate was about 100.0%, which was excellent in resilience compared to the 85.0% strain recovery rate in the previous study.

Claims (11)

A shape memory polymer comprising a repeating unit represented by the following Formula 1:
[Formula 1]

(In Formula 1,
R ₁ is a linear or branched C18 to C25 alkyl group or a linear or branched C18 to C25 hydroxy alkyl group,
R ₂ is HOC(=O)(CH ₂ ) ₈ -C(=O)O-, CH ₃ (CH ₂ )rCOO-(17≤r≤25), or -[A]a-[B]b- [C]c, wherein A is -OC(=O)(CH ₂ ) ₈ -C(=O)O- or HOC(=O)(CH ₂ ) ₈ -C(=O)O-, and B Is -CH ₂ -CH(OH)CH ₂ -or HOCH ₂ -CH(OH)CH ₂ -, and C is -(CH ₂ )rCOO- or CH ₃ (CH ₂ )rCOO-(18≤r≤20) And, 1≤a≤10, 1≤b≤10, and 0≤c≤10,
n is an integer from 1 to 100.)
The method of claim 1,
R ₁ is a linear or branched C18 to C20 alkyl group or a linear or branched C18 to C20 hydroxy alkyl group,
R ₂ is HOC(=O)(CH ₂ ) ₈ -C(=O)O-, CH ₃ (CH ₂ )rCOO-(18≤r≤25), or -[A]a-[B]b- [C]c, wherein A is -OC(=O)(CH ₂ ) ₈ -C(=O)O- or HOC(=O)(CH ₂ ) ₈ -C(=O)O-, and B Is -CH ₂ -CH(OH)CH ₂ -or HOCH ₂ -CH(OH)CH ₂ -, and C is -(CH ₂ )rCOO- or CH ₃ (CH ₂ )rCOO-(18≤r≤20) And, 1≤a≤5, 1≤b≤5, and 1≤c≤5, -[A]a-[B]b-[C]c has a randomly connected structure,
n is an integer of 5 to 70, shape memory polymer.
delete The method of claim 1,
The shape memory polymer has a weight average molecular weight of 500 to 5,000 g/mol, shape memory polymer.
The method of claim 1,
The shape memory polymer has an elongation of 40% or more after heat curing,
A shape memory polymer having a strain recovery rate of 80 to 100%.
The method of claim 1,
The shape memory polymer has a melting point of 7 to 40 ℃ after thermal crosslinking, the shape memory polymer.
As shown in Scheme 1 below,
(a) reacting the compound of formula 3 with the compound of formula 4; And
(b) reacting the obtained polymer of formula 5 with the compound of formula 6; a method for producing a shape memory polymer represented by formula 1, including:
[Scheme 1]

(In the above Scheme 1,
R ₁ is a linear or branched C6 to C25 alkyl group or a linear or branched C6 to C25 hydroxy alkyl group,
R ₂ is HOC(=O)(CH ₂ ) ₈ -C(=O)O-, CH ₃ (CH ₂ )rCOO-(6≤r≤25), or -[A]a-[B]b- [C]c, wherein A is -OC(=O)(CH ₂ ) ₈ -C(=O)O- or HOC(=O)(CH ₂ ) ₈ -C(=O)O-, and B Is -CH ₂ -CH(OH)CH ₂ -or HOCH ₂ -CH(OH)CH ₂ -, and C is -(CH ₂ )rCOO- or CH ₃ (CH ₂ )rCOO-(8≤r≤20) And, 1≤a≤10, 1≤b≤10, and 0≤c≤10,
n is an integer from 1 to 100.)
The method of claim 7,
The compound of Formula 6 is Caprylic acid, Capric acid, Undecanoic acid, Lauric acid, Tridecanoic acid, Myristic acid. ), Pentadecanoic acid, Palmitic acid, Palmitoleic acid, Heptadecanoic acid, Stearic acid, Oleic acid, Ricinoleic acid (Ricinoleic acid), Linoleic acid, Arachidic acid, Arachidonic acid, Tricosanoic acid, Erucic acid, Behenic acid , Lignoceric acid (Lignoceric acid), and one or more selected from the group consisting of nervonic acid (Nervonic acid), a method for producing a shape memory polymer.
The method of claim 7,
The shape memory polymer further performs a thermal crosslinking reaction, a method of manufacturing a shape memory polymer.
A medical material comprising the shape memory polymer according to any one of claims 1 to 6.
The method of claim 10,
The medical material is a stent, a tissue adhesive, a tissue suture, a hemostatic agent, an anti-adhesion agent, or a medical material that is a tissue engineering support.

Images