阅读说明：本技术 一种可降解泪管栓及其制备方法与应用 (Degradable lacrimal duct suppository and preparation method and application thereof ) 是由 张志兵 左保燕 陶秀梅 陈鹏 尚丽霞 于 2019-09-27 设计创作，主要内容包括：本发明涉及医药技术领域,具体公开了一种可降解泪管栓及其制备方法与应用。本发明的制备可降解泪管栓的方法,包括先将含聚乙二醇衍生物的组分A置入第一物料通道,将含三赖氨酸醋酸盐的组分B置入第二物料通道,然后将所述组分A与所述组分B分别从所述第一物料通道与所述第二物料通道中挤出到同一混合通道中进行静态混合以形成水凝胶,待所述水凝胶干燥后进行加热拉伸。该方法采用连续微观混合方式,可即混即灌,灌注过程不受凝胶化时间影响,使产品不产生气泡,质量均一；且采用干凝胶热拉伸方法,无需吸湿和二次再干燥,工艺简单。本发明的可降解泪管栓由上述方法制备得到,其不含气泡,外观光滑,质量均一,适于应用于治疗干眼症的器械。(The invention relates to the technical field of medicines, and particularly discloses a degradable lacrimal duct suppository, and a preparation method and application thereof. The method for preparing the degradable lacrimal duct suppository comprises the steps of firstly placing a component A containing polyethylene glycol derivatives into a first material channel, placing a component B containing trilysine acetate into a second material channel, then extruding the component A and the component B from the first material channel and the second material channel respectively into the same mixed channel for static mixing to form hydrogel, and heating and stretching after the hydrogel is dried. The method adopts a continuous micro mixing mode, and can realize mixing and filling, and the filling process is not influenced by gelation time, so that the product does not generate bubbles and has uniform quality; and a xerogel hot stretching method is adopted, moisture absorption and secondary re-drying are not needed, and the process is simple. The degradable lacrimal duct suppository is prepared by the method, does not contain bubbles, has smooth appearance and uniform quality, and is suitable for being applied to instruments for treating xerophthalmia.)

1. A method for preparing a degradable lacrimal duct suppository is characterized by comprising the steps of firstly placing a component A containing polyethylene glycol derivatives into a first material channel, placing a component B containing trilysine acetate into a second material channel, then extruding the component A and the component B from the first material channel and the second material channel respectively into the same mixing channel for static mixing to form hydrogel, and heating and stretching after the hydrogel is dried.

2. The method according to claim 1, wherein the ratio of the speed of the component a to the speed of the component B entering the mixing channel is (2-5):1, preferably (3-4):1, and the rate of the static mixing is 10-100ml/min, preferably 30-60 ml/min.

3. The method according to claim 1 or 2, characterized in that the temperature of the heated stretching is 40-80 ℃, preferably 50-70 ℃; and/or the drawing rate of the heat drawing is 0.2 to 2.0m/s, preferably 0.6 to 1.2 m/s.

4. The method according to any one of claims 1 to 3, wherein the component A is a borax buffer containing the polyethylene glycol derivative at a concentration of 5-40% (w/v).

5. The method of any one of claims 1-4, wherein component B is a borax buffer comprising the trilysine acetate at a concentration of 1-5% (w/v).

6. The method according to any one of claims 1 to 5, wherein the mass ratio of the polyethylene glycol derivative to the trilysine acetate is (20-50): 1.

7. the method according to any one of claims 1 to 6, wherein the polyethylene glycol derivative is prepared by modifying polyethylene glycol with a group, and the group for modifying the polyethylene glycol is one or more of succinimide carbonate, succinimide glutarate, succinimide acetate, succinimide propionate, succinimide succinate, succinimide valerate, and maleimide.

8. The method according to any one of claims 1 to 7, wherein the component A and the component B respectively further comprise a color-developing agent, preferably N-hydroxysuccinimide fluorescein.

9. A degradable lacrimal plug prepared according to any of claims 1-8.

10. Use of the degradable lacrimal plug of claim 9 in a device for treating dry eye.

Technical Field

The invention relates to the technical field of medicines. In particular to a degradable lacrimal duct suppository and a preparation method and application thereof.

Background

Dry eye is a multifactorial tear and ocular surface disease that can lead to symptoms of ocular discomfort (severe dryness of the eye, foreign body sensation, dryness, burning, photophobia, tearing), impaired vision (asthenopia, blurred or fluctuating vision), instability of the tear film, and potential damage to the ocular surface, often accompanied by increased tear film osmotic pressure and inflammation of the ocular surface, with severe cases causing rapid loss of visual function and even blindness. For a long time, with the change of life and working environment of people, the popularization of computers, air pollution and other factors, the prevalence rate of dry eye is gradually increasing, and the dry eye disease becomes one of the most common diseases in the outpatient department of ophthalmology, and the onset age of the dry eye disease tends to be younger.

Current epidemiological studies have shown that about one-fifth of the us suffer from varying degrees of dry eye, and the prevalence increases significantly with age. Nearly 50% of the U.S. 35-60 year old middle-aged female population are reported to have dry eye, and 14.6% of the elderly have severe dry eye. In modern society, the incidence of dry eye is increasing due to significant changes in the living environment and manner, and has severely threatened the normal life of patients, including reading, working, driving, etc. Against this condition, the more common methods of clinical treatment of dry eye are artificial tears, punctal occlusion, and lacrimal passage embolization. Among them, the treatment method of artificial tears requires a long treatment time and is easy to recur, and only mild dry eye can be treated. Although simple and effective, the punctum is easy to scar, is accompanied by pain, and is irreversible in operation. Currently, lacrimal embolization is the best effective method for treating dry eye. The lacrimal passage embolism is a newer lacrimal duct closing technology, which reduces the tear discharge by mechanically blocking the lacrimal passage and prolongs the stay time of the lacrimal passage on the surface of the eye, so as to achieve the purposes of improving the surface environment of the eye and relieving the dry eye symptom, or prolong the time of the medicine on the surface of the eye, thereby improving the medicine treatment effect and obviously relieving the dry eye symptom of a patient.

The lacrimal passage suppository applied to clinic can be divided into two types, namely degradable type and permanent type. The permanent lacrimal passage suppository is usually made of silica gel or polyacrylate materials, and the materials are not degradable. The degradable lacrimal passage suppository mainly takes animal collagen as a raw material, can be automatically degraded in a short period (about one week) after being implanted into the lacrimal passage, and is mainly used for short-term experimental treatment and seasonal dry eye. The degradable lacrimal passage suppository has the defects of large volume, increased length and diameter, deeper implantation position, easy slipping after implantation, short maintenance time and high price after encountering tears.

In view of the above, chinese patent application CN109077993A discloses a lacrimal duct slow-release hydrogel implant and a preparation method thereof to address the above-mentioned drawbacks, the implant adopts PEG derivative material as a carrier, and has a function of lacrimal duct embolism in form as well as a drug-loading effect. The implant has intelligent characteristics, can automatically shorten and thicken after meeting water, can retract into the deep part of a lacrimal duct, and effectively avoids slipping, but the preparation method of the implant relates to secondary drying, and the production period is longer. In addition, in the preparation process, polyethylene glycol (PEG) derivatives and the trilysine acetate phase are mixed in advance, and bubbles are generated in a mixed system in the preparation process. And because the cross-linking reaction occurs immediately after mixing, the viscosity is gradually increased, and once the gel is formed, the fluidity is lost, and subsequent filling can not be carried out any more, therefore, the gel needs to be quickly and uniformly mixed and quickly filled, so that air bubbles can not be eliminated and exist in the gel, the phenomenon that the surface of part of dried gel prepared after vacuum drying is uneven is caused, and the uniformity of the product is influenced. And the subsequent hydrogel stretching requires secondary drying, which is not favorable for industrial production.

Therefore, it is desirable to provide a new degradable lacrimal plug and a preparation method and application thereof to solve the problems of the prior art.

Disclosure of Invention

In order to solve the problems in the prior art, the invention aims to provide a preparation method of a degradable lacrimal duct suppository, which has short production period and uniform product quality.

In order to realize the purpose of the invention, the technical scheme of the invention is as follows:

a method for preparing a degradable lacrimal duct suppository comprises the steps of firstly placing a component A containing polyethylene glycol derivatives into a first material channel, placing a component B containing trilysine acetate into a second material channel, then extruding the component A and the component B from the first material channel and the second material channel respectively into the same mixed channel for static mixing to form hydrogel, and heating and stretching after the hydrogel is dried.

When the lacrimal duct suppository is prepared conventionally, the gel contains air after the polyethylene glycol derivative and the trilysine acetate are mixed, so that the dried gel prepared after vacuum drying has uneven surfaces, and uniform products cannot be obtained. The preparation method of the invention can avoid the mixing of air bubbles, greatly improves the quality uniformity of the product, and the polyethylene glycol derivative phase and the trilysine acetate phase are not required to be mixed together totally, but are gradually micro-mixed along with the continuous extrusion of the two phases from the material channel, and the mixing volume is small, so the mixing efficiency is high, the uniformity is good, the mixing can be carried out as soon as pouring, and the whole process is not influenced by the gelation time.

In addition, researches show that the chemical crosslinking gel prepared by the method can be suitable for direct heating and stretching treatment after being dried, has good stretching performance and uniform stress on the whole gel, so that the prepared xerogel can be rapidly, simply and conveniently stretched and formed, and the problems that the conventional xerogel is poor in stretching performance, easy to break at two ends in the drying process and difficult to keep in a stretching state when being stretched in a silicone tube, the xerogel is difficult to take out and cut after the silicone tube retracts, the batch-to-batch difference is large, the industrial production is difficult and the like are solved. Compared with the existing mode that the hydrogel is dried and then taken out, placed in a high-humidity environment for stretching and then dried, the secondary drying is avoided, the production period is shortened, and the production cost is saved.

In the method, the drying temperature of the hydrogel is 60-80 ℃, and the drying time is 4-8 h.

The continuous mixing mode of the polyethylene glycol derivative solution and the trilysine acetate solution can be carried out by adopting a duplex syringe (duplex medicine mixer) or a microchannel reactor. The microchannel reactor may be T-shaped or Y-shaped, with a channel diameter or width of 0.1-2.0mm, preferably 0.4-1.0mm, to allow easier control of the mixing rate.

In the method, the speed ratio of the component A to the component B entering the mixing channel is (2-5):1, preferably (3-4):1, so that the gel cross-linked space network structure is more uniform, and the diameter uniformity of the subsequent dried gel during heating and stretching is further ensured. The static mixing rate is 10-100ml/min, preferably 30-60ml/min, to facilitate uniform mixing.

The mixing of the component A and the component B can be directly carried out at normal temperature.

In the method of the present invention, the temperature for the heat stretching is 40 to 80 ℃, preferably 50 to 70 ℃.

If the heating temperature of the xerogel is lower than 40 ℃, the xerogel cannot be fully softened and cannot be effectively stretched, while if the heating temperature is higher than 80 ℃, the xerogel is too soft and has poor pressure resistance, and two ends of the xerogel are easy to break in the fixing process and cannot be stretched.

In the method of the present invention, the stretching rate of the heat stretching is 0.2 to 2.0m/s, preferably 0.6 to 1.2m/s, so that a xerogel having a more uniform diameter can be obtained during stretching.

In the method of the present invention, the stretching ratio of the heating stretching is 1 to 5 times.

In the method, the component A is borax buffer solution containing the polyethylene glycol derivative, and the concentration of the polyethylene glycol derivative is 5-40% (w/v).

In the method, the component B is borax buffer solution containing the trilysine acetate, and the concentration of the trilysine acetate is 1-5% (w/v).

In the method, the mass ratio of the polyethylene glycol derivative to the trilysine acetate is (20-50): 1.

in a preferred embodiment of the present invention, the concentration of the polyethylene glycol derivative in the component a is 30% (w/v), the concentration of the trilysine acetate in the component B is 3% (w/v), and the mass ratio of the polyethylene glycol derivative to the trilysine acetate is 30: 1.

in the method, the concentration of the borax buffer solution is 0.005-0.05mol/L, and preferably 0.01-0.03 mol/L. The gelation time of the invention can be adjusted by adjusting the concentration of borax buffer solution, and in an optimal range, the time for forming gel after the component A and the component B are mixed can be controlled within 3-10 min, the gelation time of the system is too long when the concentration is too low, and the gelation time is too short when the concentration is too high, which is not beneficial to the control of production.

By adjusting the type and the dosage of the polyethylene glycol derivative, the spatial crosslinking density and the strength can be adjusted, so that the degradation period of the lacrimal duct suppository can be adjusted to 3-90 days.

In the method, the polyethylene glycol derivative is prepared by modifying polyethylene glycol with groups, and the groups for modifying the polyethylene glycol are one or more of succinimide carbonate-SC, succinimide glutarate-SG, succinimide acetate-SCM, succinimide propionate-SPA, succinimide succinate-SS, succinimide valerate-SVA and maleic imide-MAL.

In the method, the molecular weight of the polyethylene glycol derivative is 5000-50000.

In the method, the component A and the component B both comprise color developing agents, and the content of the color developing agents in the component A and the component B is 0.02-0.2% (w/v).

In the method of the invention, the colour developer is a non-toxic coloured substance suitable for use in an implantable medical device; preferably N-hydroxysuccinimide fluorescein.

The non-toxic colored substance may be one or more of FD & C BLUE #1, FD & C BLUE #2, eosin, fluorescein, methylene BLUE, indocyanine green, N-hydroxysuccinimide fluorescein.

When N-hydroxysuccinimide fluorescein is used, the color will disappear only after the gel is completely degraded, because it can participate in the crosslinking reaction of the hydrogel. It does not decrease the color developing effect with the tear loss, compared to a color developing agent existing in a gel in a free molecular or ionic state.

In the method of the present invention, the ophthalmic drug may be dissolved or dispersed in the component a or the component B to have an anti-inflammatory or anti-glaucoma effect. The ophthalmic medicine can be one or more selected from travoprost, latanoprost, cyclosporine, gatifloxacin, prednisolone, ibuprofen, dexamethasone, tobramycin, timolol and atropine.

The method for preparing the degradable lacrimal duct suppository (lacrimal duct slow-release hydrogel implant) specifically comprises the following steps:

(1) dissolving a polyethylene glycol derivative in a borax buffer solution containing a color developing agent, and transferring the solution into an injector of a duplex medicine mixer;

(2) dissolving trilysine acetate in borax buffer solution containing a color developing agent, and transferring the solution into the other injector of the duplex medicine mixer;

(3) pushing the duplex medicine mixer, and immediately filling the mixed solution into the silica gel tube;

(4) standing the silica gel tube to form hydrogel, and then drying the hydrogel in vacuum to constant weight;

(5) drawing out the xerogel from the silicone tube, heating to soften, and stretching (by adopting a stretching instrument);

(6) naturally cooling the stretched gel to room temperature, and cutting to obtain the lacrimal duct suppository.

Another object of the present invention is to provide a rod-shaped intelligent degradable lacrimal duct plug which can automatically shorten and thicken after being inserted into lacrimal canaliculus.

The degradable lacrimal duct suppository is prepared by the method.

The degradable lacrimal duct suppository matrix material is polyethylene glycol derivative and trilysine acetate. The diameter of the lacrimal duct plug is 0.3-0.5mm, preferably 0.35-0.45 mm; the length is 2-6mm, preferably 3-5 mm; the diameter of the lacrimal duct can be expanded to 0.8-2.0mm, preferably 1.0-1.5mm, the length of the lacrimal duct can be shortened by 10-60%, preferably 20-40%, the lacrimal duct can be retracted into the deep part of the lacrimal duct, and the lacrimal duct can be effectively prevented from slipping off.

Still another object of the present invention is to provide a use of the above degradable lacrimal duct suppository in an apparatus for treating dry eye.

The invention has the beneficial effects that:

(1) the xerogel heating stretching method is adopted, after stretching, only natural cooling is needed to be carried out to the room temperature, moisture absorption and secondary drying are not needed, and the production period is shortened.

(2) The preparation method of the invention ensures that the polyethylene glycol derivative phase and the trilysine acetate phase do not need to be totally mixed in advance, but are injected respectively through two phases to be microscopically mixed at an intersection, the mixing efficiency is high, the uniformity is good, the mixing and filling can be carried out, the whole process is not influenced by the gelation time, meanwhile, the product does not generate bubbles, the quality becomes uniform, and the preparation method is suitable for hot stretching preparation.

(3) The degradable lacrimal duct suppository prepared by the invention does not contain bubbles, has smooth appearance and uniform and stable quality.

(4) The degradable lacrimal duct suppository prepared by the invention can be applied to instruments for treating xerophthalmia, improves the ocular surface environment and relieves xerophthalmia.

Detailed Description

Preferred embodiments of the present invention will be described in detail with reference to the following examples. It is to be understood that the following examples are given for illustrative purposes only and are not intended to limit the scope of the present invention. Various modifications and alterations of this invention will become apparent to those skilled in the art without departing from the spirit and scope of this invention.

The experimental procedures used in the following examples are all conventional procedures unless otherwise specified. Materials, reagents and the like used in the following examples are commercially available unless otherwise specified.