Method for making stent for radiation therapy of bile duct malignancies

FIELD: medicine.

SUBSTANCE: invention refers to nuclear medical equipment and relates to the development of a method for making polyethylene and Teflon biliary stents provided with a radionuclide-containing segment and applicable for endoscopic implantation into a bile duct for the purpose of radiation therapy of the malignancies. Making said stents involves the following stages: 1) preparing a three-layer membrane consisting of polyethylene or Teflon outer layer and an inner layer made of a composite sorbent of polyethylene or Teflon as a matrix, and ionite as an excipient, 2) fixation of a radionuclide in the inner layer of the membrane by filtration of an aqueous-alcohol radionuclide-containing solution, 3) washing of the membrane in the aqueous-alcohol solution, 4) drying of the membrane, 5) extrusion of the three-layer membrane.

EFFECT: method provides the reliable fixation of the radionuclide in the matrix of the polymer stent without disturbing a thickness homogeneity of the stent and eliminates an ability of radioactive segment destruction in the radiotherapy.

5 cl, 4 ex

 

The invention relates to the field of nuclear medical equipment and, in particular, is associated with the creation of polyethylene and Teflon biliary stents are tubular type for implantation into the bile duct with the aim of radiation therapy of malignant tumors and simultaneous normalization draining function of the bile duct.

In modern biliary endoscopy is the most widely used Soehendra stent-Tannenbaum made from Teflon and polyethylene. [Soehendra N., Reinders-Frederix V. Palliative biliary duct drainage. A new method for endoscopic introduction of a new drain]. Dtsch. Med. Wochenschr. 1979, 104(6); 206-207], [Catalano M.F., Geenen J.E., Lehman, G.A., et al., “Tannenbaum” Teflon stents versus traditional polyethylene stents for treatment of malignant biliary stricture. [Gastrointest. Endosc., 2002, 55(3), 354-358].

Currently, the global market for medical equipment offers a wide standardized set of these stents. These stents are extremely affordable and are easily replaced when they boonratana, and in the case of proximal and distal migration of the bile duct. Along with polymeric stents currently in biliary endoscopy is also used self-expanding metal stents. As polymeric stents, metallic stents are boonratana and require periodic replacement. Self-expanding metal stents significantly more expensive, harder to use and currently in biliary endoscopy game is tons of secondary importance.

The main trend of modernization of biliary stents are intended to combine their drainage capacity with additional therapeutic effects, among which an important place is occupied by radiation therapy.

Closest to the proposed invention is a method of manufacturing a stent for radiation therapy of tumors of the bile duct, as claimed in the patent [United States Patent 6,152,869, IC: A61N 5/10 (20060101); A61F 2/06 (20060101); A61N 005/00]. In this method, the radionuclide is injected into the matrix separately manufactured polymer coupling, which is then put on the standard expanding metal stent and fixed using adhesives.

Radioactive polymer coupler is manufactured as follows. The nitrate solution of radionuclide (I-131, Y-90, Co-60, Re-188, and others) in an organic solvent is injected into the organic solution of the polymer (e.g. polyurethane, utilizating rubber and others) in a volatile organic solvent. Received radionuklidami the polymer solution is applied on the inner surface of a rotating heated glass tube, the walls of which after evaporation of the organic solvent is formed of elastic radioactive polymer tube (sleeve). The clutch is separated from the wall of the glass tube, remove and cut off a segment of the desired size. After washing and drying radioactive p is the polymer coupler is put on the standard expanding metal stent and stick to the metal surface in the place of the stent, which corresponds to the location of the tumor. Radioactive stent manufactured by the above method, is designed for implantation in the bile duct for conducting radiation therapy of tumors while maintaining the drainage capacity of the duct.

The clutch causes the stent of number of drawbacks. A significant disadvantage is the thickening of the stent in placement of the coupling, which leads to heterogeneity profile of the stent, the emergence of difficulties in implantation and removal. In addition, generated by coupling a local thickening of the wall of the stent makes it necessary to reduce the internal diameter of the tube, which weakens its draining capacity.

The disadvantage of the method of manufacturing a stent is a need for gluing radioactive coupling to the metal that is technologically difficult and carries the risk of detachment of the coupling from the metal surface of the stent under the action of bile and microorganisms.

Another disadvantage of the method of manufacturing the specified radioactive stent is the difficulty of obtaining a homogeneous cylindrical coupling from podsiadlo solution of the polymer due to uneven spreading of a viscous polymer mass during evaporation of the solvent. Also used in the prototype, the introduction of a radionuclide in a polymeric material in f is RME soluble salts creates potential conditions for increased leaching of radionuclide.

In addition to these shortcomings, the solution proposed in the method prototype is not suitable for fixation of radionuclides on standard commercial polyethylene and Teflon biliary stents. For polyethylene and Teflon no effective organic solvents and adhesive compositions that provide anchorage of the polymer radioactive clutch on their surface.

The objective of the invention is to develop a method, a solid fixation of a radionuclide in a particular segment of polyethylene or Teflon biliary stents.

The problem is solved by providing stents made of polyethylene or Teflon radioactive segment located at the desired location of the stent and containing volumetrically distributed radionuclide with a desired radiation energy and dose while maintaining the uniform thickness of the stent.

As radionuclides can be used radionuclides, selected from the series: I-131, I-125, Au-198, Ir-192, Co-60, Ho-166, Yb-169, Pd-103, Pd-109, Sm-153, Dy-165 Er-169, P-32, Y-90, Re-186, Re-188. The choice of a radionuclide is determined by the half-life and radiation energy required for radiotherapy.

The solution of this problem is as follows. Radionuklidami the solution is filtered through a triple-layered membrane consisting of outer polyethylene or Teflon layer and the inner layer comp is salonaho sorbent based on polyethylene or Teflon as a matrix and the ion exchange resin as a filler. At this stage, the radionuclide quantitatively localized in the inner membrane layer. Three-layer membrane is washed with a water-alcohol solution at a ratio of water:alcohol 1:(1-0 .7), dried and subjected to extrusion, resulting in the formation of polyethylene or Teflon tube containing the radioactive segment. In the case of Teflon stent into force necessary annealing as filler composite sorbent use of inorganic ion exchangers with weight content of 5-10%. In the case of polyethylene stent filler composite sorbent can be both inorganic and organic ion exchanger with weight content of 5-10%. Strong sorption of the radionuclide on the ion exchanger, together with its mechanical insulation molded in a polymeric matrix of polyethylene or Teflon create an effective barrier against leaching of radionuclides from the stent in contact with the physiologically-active liquid environments.

Unlike the prototype, stents made of this technology, have a uniform smooth surface that facilitates endoscopic implantation and extraction of the bile duct. In the manufacture of the stent radioactive segment formed in the stent, which corresponds to the location of the tumor, which provides the best conditions for a wireless gamepad, the FIPA and optimizes exposure to healthy tissue. In case you need to interrupt radiotherapy procedure, the radioactive stent remove and replace inactive stent. Unlike the prototype, in the manufacture of the proposed stent are not formed radioactive waste.

The developed technology of radionuclide localization in a certain segment of the polymer biliary stent using ion exchangers applies to both cationic and anionic forms of the radionuclides. Below are examples of the manufacture of Teflon and polyethylene stents containing radioactive segment radionuclides131I [T1/2=8.04 days., β (0.606 MeV), γ (0.364 MeV)]90Y [T1/2=2.7 days., β (2.288 MeV), γ (1,761 MeV)].

Example 1

A portion of the fine PTFE powder with a particle size of 1-2 microns (300 mg) is placed at the bottom of the mold made of stainless steel (internal diameter 1 cm), equipped with a removable filter bottom and punch. Placed in the cylinder of Teflon powder is compacted prior to the formation at the bottom of the mold layer thickness 5-6 mm After that, the mold is placed a portion (300 mg) prepared separately homogeneous mixture of 290 mg of fine Teflon (1-2 μm) and 10 mg melkorazdroblennyh (1-2 μm) of zeolite in Ag+-form. Made the mixture is compacted to a total thickness (together with the lower layer) 9-10 mm. Then the mold is placed a portion (300 mg) milked spirtnogo Teflon (1-2 µm) and the powder in the mold is compacted to a thickness of 14-15 mm. As a result of these operations in the mold is formed of three-layer porous membrane thickness of 14-15 mm, consisting of an outer Teflon layer and the inner layer of the composite sorbent on the basis of Teflon as a matrix and zeolite Ag+form as filler.

In the mold, containing the three-layered membrane, pour 10 ml of water-ethanol mixture (1:1), incubated for one hour and the solution is poured through the filter bottom. After complete draining of the leaching solution in a three-layer membrane is applied to the aliquot of a neutral water-alcohol solution containing 20 MBq131I in the form of iodide anion, add 5 ml of ethanol-water mixture and filtered at a rate of ~0.1 ml/min until complete draining of the filtrate. At this stage quantitative binding131I on the sorbent in the inner layer of the membrane. The membrane was washed with 5 ml of water-ethanol mixture and dried by passing through it a stream of dry warm air at a rate of ~10 l/h. In the dried membrane with cylindrical knife cut through the coaxial channel with a diameter of 2.5 mm, remove the bottom cover of the mold, the membrane being ousted from using a punch and mounted on the mandrel of the extruder. Obtained by extrusion Teflon tube with radioactive segment cut off from both ends to the desired length (10 cm)slices pagevault timepressure and on both sides of the tube at a distance of 1 cm from the edges of cutting the anchor wings. The resulting billet is placed in a glass tube annealing, the configuration of which (the curvature) is identical to the configuration of the Soehendra stent-Tannenbaum TTSO-10-9. The product is maintained at a temperature of 350°C for three hours and slowly cooled. As a result of annealing the stent takes the desired curvature. After cooling the stent successively washed with diluted sodium thiosulfate solution and with distilled water and then dried. The distance between the ends of a flattened stent is 10 cm Distance between the ends of the curved stent 9 see External and internal tube diameter of the stent - 3.3 and 2.9 mm, respectively. Almost all the activity131I (~99%) is concentrated in the three-segment, located in the middle of the stent. The rate of leaching131I from the stent bile (100 ml) under static conditions is 0.05% per day.

Example 2

Portion of fine polyethylene powder with a particle size of 1-2 microns (300 mg) is placed at the bottom of the mold made of stainless steel (internal diameter 1 cm), equipped with a removable filter bottom and punch. Placed in the cylinder of polyethylene powder is compacted prior to the formation at the bottom of the mold layer thickness of 5-6 mm, then the cylinder is placed a portion (300 mg) prepared separately homogeneous mixture of 290 mg of fine polyethylene (1-2 μm) and 10 mg is melkorazdroblennyh (1-2 μm) of cation exchange resin KU-2 Ag +-form. The mixture is compacted to a total thickness (together with the lower layer) 9-10 mm. Then the mold is placed a portion (300 mg) fine polyethylene (1-2 µm) and the powder in the mold is compacted to a thickness of 14-15 mm as a result of these operations in the mold is formed of three-layer porous membrane thickness of 14-15 mm, consisting of an outer plastic layer and an inner layer of the composite sorbent on the basis of polyethylene as a matrix and fine cation exchange resin KU-2 Ag+form as filler.

In the mold, containing the three-layered membrane, pour 10 ml of water-ethanol mixture (1:1), incubated for one hour and the solution is poured through the filter bottom. After complete draining of the leaching solution on the membrane is applied to the aliquot of a neutral water-alcohol solution containing 20 MBq131I in the form of iodide anion, add 5 ml of ethanol-water mixture and filtered at a rate of ~0.1 ml/min until complete draining of the filtrate. At this stage quantitative binding131I on the inner layer of the membrane. The membrane was washed with 5 ml of water-ethanol mixture and dried by passing through it a stream of dry warm air at a rate of ~10 l/h. In the dried membrane with cylindrical knife cut through the coaxial channel with a diameter of 2.5 mm, remove the bottom cover cyl the echoes, the membrane is extruded from the cylinder using a punch and mounted on the mandrel of the extruder. Obtained by extruding a plastic tube with a radioactive segment cut off from both ends to the desired length (10 cm)slices smooth timepressure and on both sides of the tube at a distance of 1 cm from the edges of cutting the anchor wings. A polyethylene tube obtained by extrusion, placed in a glass tube annealing, the configuration of which (the curvature) is identical to the configuration of the Soehendra stent-Tannenbaum TTSO-10-9. The product is maintained at a temperature of 80°C for one hour and slowly cooled. As a result of annealing the stent takes the desired curvature. After cooling the stent successively washed with diluted sodium thiosulfate solution and with distilled water and then dried. The distance between the ends of a flattened stent equals 10 cm Distance between the ends of the curved stent 9 see External and internal tube diameter of the stent - 3.3 and 2.9 mm, respectively. Almost all the activity131I (~99%) is concentrated in the three-segment, located in the middle of the stent. The rate of leaching131I from the stent bile (100 ml) under static conditions is 0.03% per day.

Example 3

A portion of the fine PTFE powder with a particle size of 1-2 microns (300 mg) is placed at the bottom of the mold of the modern is her steel (internal diameter 1 cm), equipped with a removable filter bottom and punch. Placed in the cylinder of Teflon powder is compacted prior to the formation at the bottom of the mold layer thickness 5-6 mm After that, the mold is placed a portion (300 mg) prepared separately homogeneous mixture of 290 mg of fine Teflon (1-2 μm) and 10 mg melkorazdroblennyh (1-2 μm) of the zeolite in the H+-form. Made the mixture is compacted to a total thickness (together with the lower layer) 9-10 mm. Then the mold is placed a portion (300 mg) fine Teflon (1-2 µm) and the powder in the mold is compacted to a thickness of 14-15 mm as a result of these operations in the mold is formed of three-layer porous membrane thickness of 14-15 mm, consisting of an outer Teflon layer and the inner layer of the composite sorbent on the basis of Teflon as a matrix and zeolite as filler.

In the mold, containing the three-layered membrane, pour 10 ml of water-ethanol mixture (1:1), incubated for one hour and the solution is poured through the filter bottom. After complete draining of the leaching solution in a three-layer membrane is applied to the aliquot of a neutral water-alcohol solution containing 20 MBq90Y, add 5 ml of ethanol-water mixture and filtered at a rate of ~0.1 ml/min until complete draining of the filtrate. At this stage quantitative binding90Y SOR is ence in the inner layer of the membrane. The membrane was washed with 5 ml of water-ethanol mixture and dried by passing through it a stream of dry warm air at a rate of ~10 l/h. In the dried membrane with cylindrical knife cut through the coaxial channel with a diameter of 2.5 mm, remove the bottom cover of the mold, the membrane is extruded from the cylinder using a punch and mounted on the mandrel of the extruder. Obtained by extrusion Teflon tube with radioactive segment cut off from both ends to the desired length (10 cm)slices smooth timepressure and on both sides of the tube at a distance of 1 cm from the edges of cutting the anchor wings. The resulting billet is placed in a glass tube annealing, the configuration of which (the curvature) is identical to the configuration of the Soehendra stent-Tannenbaum TTSO-10-9. The product is maintained at a temperature of 350°C for three hours and slowly cooled. As a result of annealing the stent takes the desired curvature. After cooling the stent successively washed with diluted sodium thiosulfate solution and with distilled water and then dried. The distance between the ends of a flattened stent is 10 cm Distance between the ends of the curved stent 9 see External and internal tube diameter of the stent - 3.3 and 2.9 mm, respectively. Almost all the activity90Y (~99%) is concentrated in the three-segment, located in the middle of the stent. The rate of leaching131I from the stent bile (100 ml) under static conditions is 0.05% per day.

Example 4

Portion of fine polyethylene powder with a particle size of 1-2 microns (300 mg) is placed at the bottom of the mold made of stainless steel (internal diameter 1 cm), equipped with a removable filter bottom and punch. Placed in the cylinder of polyethylene powder is compacted prior to the formation at the bottom of the mold layer thickness of 5-6 mm, then the cylinder is placed a portion (300 mg) prepared separately homogeneous mixture of 290 mg of fine polyethylene (1-2 μm) and 10 mg melkorazdroblennyh (1-2 μm) of cation exchange resin KU-2 in the N+-form. The mixture is compacted to a total thickness (together with the lower layer) 9-10 mm. Then the mold is placed a portion (300 mg) fine polyethylene (1-2 µm) and the powder in the mold is compacted to a thickness of 14-15 mm as a result of these operations in the mold is formed of three-layer porous membrane thickness of 14-15 mm, consisting of an outer plastic layer and an inner layer of the composite sorbent on the basis of polyethylene as a matrix and fine cation exchange resin KU-2 as filler.

In the mold, containing the three-layered membrane, pour 10 ml of water-ethanol mixture (1:1), incubated for one hour and the solution is poured through the filter bottom. After polnomotchija leaching solution on the membrane is applied to the aliquot of a neutral water-alcohol solution, with 20 MBq90Y, add 5 ml of ethanol-water mixture and filtered at a rate of ~0.1 ml/min until complete draining of the filtrate. At this stage quantitative binding90Y sorbent in the inner layer of the membrane. The membrane was washed with 5 ml of water-ethanol mixture and dried by passing through it a stream of dry warm air at a rate of ~10 l/h. In the dried membrane with cylindrical knife cut through the coaxial channel with a diameter of 2.5 mm, remove the bottom cover of the cylinder, the membrane is extruded from the cylinder using a punch and mounted on the mandrel of the extruder. Obtained by extruding a plastic tube with a radioactive segment cut off from both ends to the desired length (10 cm)slices smooth timepressure and on both sides of the tube at a distance of 1 cm from the edges of cutting the anchor wings. A polyethylene tube obtained by extrusion, placed in a glass tube annealing, the configuration of which (the curvature) is identical to the configuration of the Soehendra stent-Tannenbaum TTSO-10-9. The product is maintained at a temperature of 80°C for one hour and slowly cooled. As a result of annealing the stent takes the desired curvature. After cooling the stent successively washed with diluted sodium thiosulfate solution and with distilled water and then dried. The distance between the ends of the races is ramlinga stent is 10 see The distance between the ends of the curved stent 9 see External and internal tube diameter of the stent - 3.3 and 2.9 mm, respectively. Almost all the activity90Y (~99%) is concentrated in the three-segment, located in the middle of the stent. The rate of leaching90Y of the stent bile (100 ml) under static conditions amounted to 0.04% per day.

1. A method of manufacturing a stent for radiation therapy of malignant tumors of the bile duct, including the introduction of the radionuclide in the polymer-containing segment of the stent, wherein radionuklidami the solution is filtered through a triple-layered membrane consisting of outer polyethylene or Teflon layer and the inner layer of the composite sorbents based on polyethylene or Teflon as a matrix and the ion exchange resin as a filler for fixing the radionuclide, after which the membrane was washed with aqueous-alcoholic solution, dried and extruded.

2. The method according to claim 1, characterized in that as radionuclide use a radionuclide selected from the range: I-131, I-125, Au-198, Ir-192, Co-60, Ho-166, Yb-169, Pd-103, Pd-109, Sm-153, Dy-165 Er-169, P-32, Y-90, Re-186, Re-188.

3. The method according to claim 1, characterized in that the washing of the membranes provide a water-alcohol solution at a ratio of water : alcohol 1:(1-0 .7).

4. The method according to claim 1, characterized in that for the manufacture of Teflon stent as the e filler composite sorbent use of inorganic ion exchangers with weight content of 5-10%.

5. The method according to claim 1, characterized in that for the manufacture of polyethylene stent as filler composite sorbent is used as inorganic and organic ion exchangers with weight content of 5-10%.



 

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10 cl, 1 ex

FIELD: medicine.

SUBSTANCE: invention refers to medicine, particularly traumatology and orthopedics, and can find application in treating false joints of long bones. What is described is a method for preparing a non-toxic porous implant of polylactic acid with controlled pore size for building of long bone defects involving melting the polylactic acid granules in a melting pot immersed in thermally stable oil with porogen presented by sodium chloride crystals 100-250 nm to be washed out by aqueous solutions of antiseptics. The implant is prepared with no toxic solvents added and has a pre-set pore diameter.

EFFECT: improved efficiency of the method.

FIELD: medicine.

SUBSTANCE: invention refers to medicine. There are described medical implanted devices made of a polymer material and a separation agent wherein the device is a cast reservoir implant, while the separation agent has a molecular weight (M.w.) of min. 1000. The separation agent can be presented by a non-ionic surfactant, such as Bridge-35, polyoxyethylene (20) sorbitan trioleate, Tween 20, Tween 80, vitamin E TPGS, and a mixture of any two or more of them. The hydrated implants can have a surface area of approximately 500 mm2 or more.

EFFECT: used separation agents causes no undesired reactions with cartridge polymer and are safely introducible in a patient.

29 cl, 5 tbl, 3 ex

FIELD: medicine.

SUBSTANCE: invention refers to medicine. High antimicrobial activity and desired smoothness providing high thromboresistance are ensured by modifying a product surface, e.g. a polyurethane polyurethane with chlorhexidine and/or its salts with the modification procedure ensured by applying 0.5-4% polyurethane of molecular weight 10000 to 40000 units. in tetrahydrofurane containing chlorhexidine and/or its salts in the amount 0.25-5% (wt) in relation to polyurethane weight that is followed by tetrahydrofurane evaporation.

EFFECT: what is described is a polyurethane catheter with antimicrobial coating, the method for preparing the antimicrobial coating on polyurethane products and the method for producing the polyurethane catheters with the antimicrobial coating.

3 cl, 1 tbl

Duraplasty graft // 2436596

FIELD: medicine.

SUBSTANCE: invention concerns medicine, particularly neurosurgery. What is disclosed is a biocompatible, biostatic, non-toxic, translucent, however imaginable, elastic, strong, reliably fastened duraplasty graft made of a spatially cross-linked polymer prepared by photopolymerisation of methacrylic oligomers. A graft represents an elastic translucent double-layer film with one layers being relieved, while the other one is smooth. The relief is blue-coloured. Such colour provides intraoperative imaging of the graft for a surgeon. At the same time, the unit dimensions of the relief drawing are such that the graft is translucent enough to control the hemostasis efficiency. The layer adjoining the brain is smooth. A roughness degree of the smooth layer ranges within 10 to 20 nanometers to eliminate the adjoining tissue ingrowth into the graft and its opacity on service.

EFFECT: improved graft performance.

7 cl, 3 dwg, 3 ex

FIELD: medicine.

SUBSTANCE: invention relates to field of medicine, in particular, to ophthalmology. For intraocular lens applied are soft, with high coefficient of reflection acrylic materials, which contain arylacrylic monomer as single main element-forming monomer, as well as macromer additive for reduction of adhesiveness.

EFFECT: invention ensures application of claimed materials in intraocular lens, as well as other ophthalmological or otolaryngological elements, such as contact lens, keratoprostheses, corneal rings, implants, otolaryngological ventilation tubes and nasal implants.

19 cl, 4 tbl, 10 ex

FIELD: medicine.

SUBSTANCE: invention relates to medicine, specifically to surgical material and means for replacement of bone tissue defects. Surgical material contains biodegradable and biocompatible copolymer of 3-hydroxybutyrate and 3-hydroxyvaleriate (3-PHB/3-PHV) and calcium phosphate substances, with the following component ratio, in wt %: copolymer 65-90 and calcium phosphate substances 10-35. According to second version, surgical material, contains biodegradable and biocompatible copolymer, calcium phosphate substances and antibiotic, selected from group which consists of tienam, gentamicin, sulperazon and rubomycinum, with the following component ratio, wt %: copolymer 65-89; calcium phosphate substances 10-35; antibiotic 1-5.

EFFECT: obtaining biodegradable and high-strength surgical material for reconstruction of bone tissue defects of various etiology, which has high osteoinductive and antimicrobial properties.

21 cl, 5 dwg, 3 tbl

FIELD: medicine, pharmaceutics.

SUBSTANCE: invention relates to application in biomedicine, cell technologies, substituting and restorative surgery, in particular for manufacturing matrix-carrier, implanted together with cells into human organism in order to restore functioning of affected organ. Method lies in preparation of solution of polyoxybutirate-polyoxyvalerate (POB/POV) in dichloroethane, after which into solution introduced is icy acetic acid with the following component ratio, g: POB/POV - 1-2, dichloroethane- 10-12, icy acetic acid - 10-15; obtained solution is frozen in form at temperature minus (25-30)°C and sublimation drying of obtained semi-product of matrix is performed in vacuum chamber. Freezing of solution and sublimation drying of obtained semi-product of matrix are performed on padding, made from polytetrafluorethylene fiber and plate from water ice. Thickness of water ice plate is selected on condition of its complete sublimation during drying in vacuum chamber, sublimation drying of matrix semi-product on padding being performed on mesh from plastic threads. Initial pressure in vacuum chamber must be not lower than 100 Torr, and after dichloroethane evaporation from matrix semi-product pressure in vacuum chamber is reduced to ~0.01 Torr. Polymer matrix with bimodal structure of simply connected pores is produced.

EFFECT: simplification and cheapening of technology due to refuse from low temperature of performing vacuum sublimation drying.

7 cl, 4 dwg

FIELD: medicine.

SUBSTANCE: invention refers to medicine, specifically to hernia surgery. A synthetic prosthesis made of monofilament fibres with a coat containing 2% chitosan of molecular weight 80000 Da, polyvinyl alcohol, a cephalosporin antibiotic or two compatible or synergistic antibiotics mixed, glycerin in a certain proportions is fixed on an aponeurosis.

EFFECT: use of the invention provides effective antibacterial agents delivery into a plasty zone and prolonged intake into the tissues, applicability of monofilament meshes as explants, reduced pyoinflammatory wound complications and recurrent hernias.

1 ex

FIELD: medicine.

SUBSTANCE: invention relates to field of medicine, namely to trachea surgery and experimental surgery. Essence of method lies in application for trachea reconstruction of tubular bioprosthesis, formed from loose skin-fascial flap on vascular pedicle, which is taken from dog's shin. After that, it is re-enforced with nitilon threads - semi-circles, which are passed by means of metal guides through subcutaneous-adipose cellular tissue.

EFFECT: application of claimed invention makes it possible to reduce intervention time, ensure bioprosthesis rigidity and eliminate possibility of development of inflammatory processes in bronchi and lungs.

3 dwg, 2 ex

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