now , examples of the invention will be explained in detail . the illustration of examples will be shown in the accompanying drawings , in which the same number represents the same or similar elements . the examples described with reference to the drawings are only illustrations , which intend for explaining the invention and do not limit the invention . with reference to fig1 to 8 , the artificial dura mater and manufacturing methods therefor are described in details below . an illustration of electrospinning process to prepare the artificial dura mater is shown in fig1 , the electrospinning sprayer 1 contains the polymer solution , the high voltage power source 3 has its high voltage end connected to the sprayer 1 . the receiving device 4 is in cylinder shape , and can be moved leftwards and / or rightwards , along with the axis of cylinder or the long shaft direction of cylinder . the movement of receiving device 4 can be set with computer program , so that the formed electrospun layer will have equal thickness . in practice , the receiving device can be set as a level - off surface , and through the movement between left and right or fore - and - aft , an even reception can be realized . the receiving device 4 is connected with the low voltage end of high voltage power source 3 , so that there is a large voltage difference between the sprayer 1 and receiving device 4 . before the electrospinning starts , the proper polymer solution for electrospinning should be prepared . it is an option to choose the solution of hydrophobic polymer for electrospinning , and such solution is prepared by dissolving a hydrophobic polymer into a solvent . wherein the hydrophobic polymer includes but not limited to the hydrophobic aliphatic polyester ( covering polylactic acid , polyglycolide , polycaprolactone , and polyhydroxybutyrate ), polyetherester ( such as polydioxanone ), polyorthoester , polyurethane , polyanhydride ( such as poly ( sebacic acid - hexadecanedioi acid anhydride )), polyphosphazene , polyamino acid and mixtures thereof . depending on the design , if the hydrophilic electrospun layer is needed after the hydrophobic electrospun layer is finished , the solution of hydrophilic polymer for electrospinning should be prepared . wherein the hydrophilic polymer includes but not limited to the chondroitine sulfate , heparin , agar , glucan , algin , modified cellulose , alginate , starch , cellulose , gelatin , fibrinogen , silk protein , elastin - mimicry peptide polymer , collagen , chitosan , modified chitosan , hydrophilic polyurethane , polyethylene glycol , polymethylmethacrylate , phbv , phbhhx , polyvinyl alcohol and polylactide . based on the actual needs , multiple sprayers 1 may be set , in which the hydrophobic polymer solution and the hydrophilic polymer solution are placed respectively . or , replace the solution in the sprayer 1 after the hydrophobic layer is made . the solvent of the solution for electrospinning can be water or a volatile organic solvent which includes but not limited to methanoic acid , acetic acid , ethyl alcohol , acetone , dimethyl formamide , dimethyl acetamide , tetrahydrofuran , dimethyl sulfoxide , hexafluoro isopropyl alcohol , trifluoroethyl alcohol , dichloromethane , trichloromethane , methyl alcohol , ethyl alcohol , chloroform , dioxane , trifluoroethane , and trifluoroacetic acid . once the solution for electrospinning is ready , the parameters should be set . after that , the power is on , and the electrospinning device is activated . as the spinning fibers 2 is spun from the sprayer 1 , the receiving device 4 will move in prescribed procedures , so as to form the uniform electrospun membrane structure . the parameters of the process to form the hydrophobic electrospun layer are set as follows : a micro - injection pump operated at a velocity of 0 . 1 - 5 . 0 milliliters / hour and a high voltage generator operated at a voltage of 5 - 40 kilovolts and with a receiving distance of 5 . 0 - 30 . 0 centimeters . the hydrophobic electrospun layer comprises fibers with a diameter , which can be controlled , ranging from 50 to 1000 μm , and pores of a size of less than 3 μm . the parameters of the process to form the hydrophilic electrospun layer are set as follows : a micro - injection pump operated at a velocity of 0 . 1 - 20 . 0 milliliters / hour and a high voltage generator operated at a voltage of 10 - 45 kilovolts and with a receiving distance of 5 . 0 - 30 . 0 centimeters . the hydrophilic electrospun layer comprises fibers with a diameter , which can be controlled , ranging from 5 to 200 μm and pores of a size of 20 - 200 μm . in practice , the above procedures can be repeated , so as to form multiple hydrophobic layers and / or multiple hydrophilic layers , as shown in fig3 and fig4 . fig3 gives an artificial dura mater with three hydrophobic layers the strength of which is similar to the human &# 39 ; s dura mater . as the layers are formed by hydrophobic materials , they are not good for the migration and attachment of cells . together with the fact that the materials are safe , poison - free and absorbable for human body , they reach the goal of anti - adhesion . fig4 gives an artificial dura mater consisting of two hydrophobic layers ( a ) and three hydrophilic layers ( b ). when the dura mater is transplanted into brain , the anti - adhesive hydrophobic layers ( a ) are set near to the brain surface , while the hydrophilic layers ( b ) are set far from the brain surface , providing a fine nanofibrous scaffold for the adhesion , migration , proliferation and differentiation of cells . as the hydrophilic layers are prepared with hydrophilic materials that offers good bio - compatibility and have larger pore size , which is good for the migration of stem cells and fibroblast , consequently , which is favorable for the growth of autologous dura mater . once the electrospun layers are made , they will be dried in an oven or in natural manner , dependent on varied solution component . when the solvent of an electrospinning solution is a volatile organic solvent , such as hexafluoro isopropyl alcohol , the procedure for dryness can be omitted since the solvent has completely volatilized while the spinning fibers 2 are spun to the receiving device 4 along with a voltage difference . as the hydrophobic layer is very different from the hydrophilic layer in the terms of hydrophilicity , the structural stability is not easy to be kept in the application . to solve such problem and increase the hydrophilicity between the two , a transition layer can be applied . the transition layer has a hydrophilicity that gradually increases from the side proximate to the hydrophobic electrospun layer to the side proximate to the hydrophilic electrospun layer . in practice , the electrospinning solution of the transition layer can comprise one or more polymers and corresponding solvent which are determined based on the requirement of hydrophilicity . then , the solution is placed into the sprayer , by the method the as above , to prepare the transition layer before the hydrophilic layer . the parameters of the process to form the transition layer are set as follows : a micro - injection pump operated at a velocity of 0 . 1 ˜ 5 . 0 milliliters / hour and a high voltage generator operated at a voltage of 5 - 40 kilovolts and with a receiving distance of 5 . 0 - 30 . 0 centimeters . the artificial dura mater with transition layer is illustrated in fig5 . in the figure , the hydrophobic layer is of two layers , and the hydrophilic layer is of three layers . between the hydrophobic layers ( a ) and the hydrophilic layers ( b ), there is a transition layer of two layers ( c ), the one , proximate to the hydrophobic layers ( a ) has a weaker hydrophilicity than the other proximate to the hydrophilic layers . furthermore , to realize the addition of cytokine and / or medicine into the artificial dura mater , a blending electrospinning can be adopted . specifically , a cytokine and / or a medicine can be blended into any one or more layers of the hydrophobic , hydrophilic and transition layers . a cytokine and / or medicine should be put into a corresponding solution . after that , the electrospinning is made and the cytokine and / or medicine will be blended into the spinning fibers 2 as the spinning fibers are formed . the membrane structure will be formed on the receiving device 4 . likewise , this procedure can be repeated . the cytokine and / or medicine added each time can be the same or different . the acquired artificial dura mater is shown in fig6 . in fig6 a , a hydrophobic layer is of a two - layer structure and a hydrophilic layer is of a three - layer structure . in fig6 b , a hydrophobic spinning fiber 7 contains a medicine 8 , and a hydrophilic spinning fiber 9 is blended with a cytokine 10 . fig7 a has two transition layers c based on fig6 . one of them proximate to the hydrophobic layer a , has a weaker hydrophilicity than that proximate to the hydrophilic layer b . from fig7 b , the hydrophobic spinning fiber 7 is blended with a medicine 8 , and the hydrophilic spinning fiber 9 is blended with a cytokine 10 , the spinning fibers of two transition layers 11 is respectively blended with medicine 8 and cytokine 9 . besides , the invention provides a method that combines electrospinning and bio - printing to prepare artificial dura mater . the bio - printing is an emerging technology , and just have been developed and applied in biomedical fields in recent years . this technology utilizes a special cell solution or a biological active solution as the “ bio - ink ” and as designed , prints precisely on the spot of a specific substrate ( termed as “ bio - paper ”) that can be degraded in the human body . after printing , the bio - papers will be stacked in certain sequence . as the printing technology is used , the bio - ink consisting of cells and / or cytokine can be precisely placed to the designed areas . the bio - papers , if stacked in particular way , will form the three dimensional structure . the specific implementation is given in fig2 . based on the device given in fig1 , the bio - printer head 5 is set , and such head can be obtained by modifying the present commercial inkjet printer as the method , for example , disclosed in u . s . pat . no . 7 , 051 , 654 . the head contains a cytokine and / or a medicine . the printing manner and printing position can be set through the computer program in advance . the specific printing procedures can base on the current technologies . in accordance with one embodiment of the invention , the cytokine and / or medicine can be enclosed in hydrogel . the hydrogel solution can be aqueous solution of polysaccharide polymer , polypeptide polymer or synthetic hydrophilic polymer . the polysaccharide polymer includes but not limited to the starch , cellulose , alginate , hyaluronic acid and chitosan . the polypeptide polymer includes but not limited to the collagen , poly - l - lysine and plga . the synthetic , hydrophilic polymer includes but not limited to polyacrylic acid , polymethacrylic acid , polyacrylamide and n - isopropyl acrylamide . the hydrogel is liquid in normal circumstances and becomes gel at certain temperature or under specific conditions . with which , the hydrogel possesses good adhesion , which can make a cytokine and / or a medicine evenly or definitely distribute on the electrostatic spinning layer . the procedures of bio - printing with hydrogel are as follows : 1 ) put the cytokine and / or medicine , prepared and blended with liquid hydrogel , into the bio - printer head 5 . 2 ) after the electrospun layer is formed , print on the electrospun layer with jet printer as per the preset program ; based on the choice of hydrogel , apply proper conditions to make the hydrogel quickly become gel / jelly that , by offering good adhesion , adhere the cytokine and / or medicine enclosed to the electrospun layers . 3 ) set even and uniform distribution of bio - ink and form the artificial dura mater as shown in fig8 a , in which , each of hydrophobic layers is printed with a layer of medicine and each of hydrophilic layers is printed with a layer of cytokine . as shown in enlarged fig8 b , the film prepared with bio - printing is different from that prepared with blending . a cytokine and / or a medicine are applied on the surface of layers that is formed by the hydrophobic spinning fiber 7 and / or the hydrophilic spinning fiber 9 . when such dura mater is transplanted into human body , the cytokine and / or medicine can be evenly released . 4 ) if necessary , set the concentrated distribution on certain points and make the cytokine and / or the medicine printed into particular areas . when such dura mater is transplanted to the human body , the cytokine and / or the medicine can be mostly released to the wanted specific areas . the solidification of some hydrogels needs a cross - linking agent to assist . in this case , a bio - printing in the utilization of hydrogel has the following procedures : 1 ) put a certain amount of cross - linking agent into the vessel 6 . once the electrospinning starts , the receiving device 4 , moving along with the axis or between left and right , will contact the agent , and the formed electrospun layers will adhere with some cross - linking agent 2 ) make the bio - printing as given above . when the liquid hydrogel inside the head 5 contacts the cross - linking agent on the electrospun layers , the hydrogel quickly turns to gel / jelly and enables the cytokine and / or medicine enclosed to adhere to the electrospun layers . the selection of cross - linking agent depends on the kind of hydrogel . for instance , when the hydrogel is sodium alginate , the cross - linking agent is calcium chloride ; when the hydrogel is fibrinogen , the agent is thrombin . according to the one embodiment of the invention , the solution of hydrophobic polymer can be hydrophobic poly ( l - lactide ) ( plla ) and ε - caprolactone dissolved to hexafluoro isopropyl alcohol or dichloromethane , the ratio of the two polymers can be 50 : 50 , 30 : 70 or 70 : 30 . as a copolymer , the number - average molecular weight is 150 , 000 - 500 , 000 . when blending is needed , the hydrophobic solution can be added with 0 . 01 - 3 % antibiotic solution and / or with 0 . 001 - 3 % medicine for hemostasis and anti - adhesion . together with the solution of poly ( l - lactide ) ( plla ) and ε - caprolactone , the final solution will be obtained . according to another embodiment of the invention , the solution of hydrophilic polymer can choose hydrophilic polyurethane plus natural gelatin , chondroitine sulfate or polyethylene glycol as solvent ( s ). the mass ratio is 20 - 80 : 80 - 20 . the spinning solution accounts for 3 - 15 % of total weight . in blending , the solution of hydrophilic polymer can be added with a solution of basic fibroblast factor , and make the concentration of cytokine of 0 . 001 - 0 . 5 %. a medicine added in blending or bio - printing can choose , in accordance with the actual situation , antibiotic or drug for hemostasis or anti - adhesion . in the transplantation of dura mater due to tumor excision , the drugs for chemotherapy of brain tumor can be added . an antibiotic includes but not limited to the cephalosporin , ampicillin , spiramycin , sulfonamides and quinolones . the first choice is ceftriaxone sodium . as meninges surgeries often need to open the skull and at present , the intracranial infection is often bacterial mainly comprising staphylococcus aureus , streptococcus , pneumococcus , escherichia coli , salmonella and pseudomonas aeruginosa . the commonest virus is staphylococcus aureus . according to the clinical reports , the ceftriaxone sodium offers better therapy effect . the anti - tumor medicine includes but not limited to nimustine , semustine , liposome doxorubicin , dactinomycin d and vincristine . the vincristine is first choice . a medicine for hemostasis or anti - adhesion can speed up the healing of wound and prevent the occurrence of adhesion . such medicine includes but not limited to the hemostasis factor ( which makes the material own the function of hemostasis ), the inhibitor of collagen synthase ( such as tranilast and pemirolast , which inhibit the revival of collagen ), the anti - coagulation drug ( such as dicoumarolum , ehparin sodium and hirudin ), the anti - inflammatory drug ( such as promethazine , dexamethasone , hydrocortisonum , prednisolone , ibuprofen and oxyphenbutazone ), the calcium channel blocker ( such as diltiazem hydrochloric , nifedipine and verapamil hydrochloride ), the cell growth inhibitor ( such as fluorouracil ), the hydrolase ( such as hyaluronidase , streptokinase , urokinase , pepsin and tpa ) and the oxidation reductant ( such as methylene blue ). according to an embodiment of the invention , in blending , the electrospinning solution is added with a cytokine and / or a medicine in this formula : the basic fibroblast growth factor accounting for 0 . 001 - 0 . 05 % of electrospinning solution weight , the ampicillin accounting for 3 % of electrospinning solution weight , the hemostasis factor accounting for 0 . 001 - 0 . 05 % of electrospinning solution weight . in a meninges restoration operation due to brain tumor , the nimustine accounting for 0 . 01 - 5 % of the weight can be added . the obtained artificial dura mater should be rinsed , sterilized , packaged and stored . poly ( l - lactide ) ( plla ) and ε - caprolactone , in the mass ratio of 50 : 50 and with number - average molecular weight of 260 , 000 , are dissolved into a solvent of hexafluoro isopropyl alcohol to form a hydrophobic electrospinning solution . put the solution into the sprayer of electrospinning . the micro - injection pump is operated at a velocity of 5 milliliter / hour ; the high voltage generator is operated at a voltage of 30 kilovolts and a receiving distance of 20 centimeters . the fibers are received to form a membrane structure and have a diameter in the average of 300 nm . after the receiving process is completed , the spinning device is closed . the artificial dura mater acquired is rinsed for five times with ethyl alcohol and distilled water . the dura mater , then , is packaged in vacuum after freeze dry . after sterilization with 25 kgy cobalt - 60 , the dura mater is stored at minus 20 ° c . the preparing method is the same as which of the example 1 . the hydrophilic solution for electrospinning choose poly ethanedioic acid and chondroitine sulfate , in the mass ratio of 70 : 30 and the mass fraction of spinning liquid is 9 %. the electrospinning device is activated , and a hydrophilic electrospun layer is formed on the hydrophobic layer already formed in embodiment 1 . the receiving distance is 11 centimeters , the voltage is 20 kilovolts , and the acquired hydrophilic layer comprises fibers in the average with a diameter of 10 μm . the rinse and store are the same as those in embodiment 1 . the hydrophobic electrospun layer is prepared in the same manner with that in embodiment 1 . the transition layer adopts a polymer solution of polyurethane and hyaluronic acid in the mass ratio of 70 : 30 and has a mass fraction of 10 %. the spinning is activated with a receiving distance of 11 centimeters and a voltage of 20 kilovolts . the fibers have a diameter at average of 5 μm . on the hydrophobic layer , the transition layer is made . then , on the transition layer , the hydrophilic layer is spun , in the same manner as that in example 4 . after that , the spinning is stopped . the rinse and store are the same as them in example 1 . ( 1 ) prepare the hydrophobic electrospun layer : choose the hydrophobic polycaprolactone and a mixed solvent of chloroform or methyl alcohol in a ratio of 1 : 1 . add with ceftriaxone sodium , at a concentration of 1 %. get the uniform solution . add the above solution into the sprayer for electrostatic spinning , and perform the electrospinning with a micro - injection pump operated at a velocity of 0 . 8 milliliters / hour and a high voltage generator operated at a voltage of 12 kilovolts and with a receiving distance of 15 centimeters . obtain the fibers in membrane structure . the fibers of the hydrophobic electrospun layer have a diameter of 600 nanometers . ( 2 ) prepare the hydrophilic electrospun layer : adopt the hydrophilic silk protein and natural gelatin in the ratio of 20 - 80 : 80 - 20 and have the mass fraction of spinning liquid at 9 %. prepare the solution of basic fibroblast factor . mix the solution with the above mentioned electrospinning solution evenly , and have the final concentration of cytokine to be 0 . 001 %, the receiving distance to be 10 cm , and the voltage to be 20 kv . start the electrospinning , and form the hydrophilic layer on the hydrophobic layer formed already . the average diameter of fibers from the hydrophilic layer is in the level of micron . the rinse and store are the same as them in example 1 . ( 1 ) prepare the hydrophobic electrospun layer : select the hydrophobic polycaprolactone and a mixed solvent of chloroform and methyl alcohol in ratio of 1 : 1 . blend with vincristine at the concentration of 100 ng / ml , and get the uniform solution . add the above solution into the sprayer for electrospinning , adjust the velocity of micro - injection pump to be 0 . 8 ml per hour , the voltage of high voltage generator to be 12 kv , and the receiving distance of receiving device to be 15 cm , and obtain the fibers in membrane structure . the fibers of the hydrophobic electrospun layer have a diameter of 600 nanometers . ( 2 ) prepare the transition layer : choose polyurethane and hyaluronic acid in the mass ratio of 70 : 30 . have the mass fraction of spinning solution at 10 %. blend with ampicillin at concentration of 3 %. the uniform solution is form . the receiving distance is 11 centimeters , the voltage is 20 kilovolts , and the average diameter of fibers is 5 μm . ( 3 ) prepare the hydrophilic electrospun layer : adopt the hydrophilic silk protein and natural gelatin in the ratio of 20 - 80 : 80 - 20 and have the mass fraction of spinning solution at 9 %. blend with ampicillin solution at a final concentration of 3 %. activate the spinning device , adjust the receiving distance to be 10 cm , and spin the hydrophilic layer on the transition layer already formed . the average diameter of fibers should be in the level of micron . the rinse and store are the same as them in example 1 . the hydrophobic solution selects the hydrophobic poly ( l - lactide ) ( plla ) and ε - caprolactone , in a mass ratio of 50 : 50 , as copolymer with a number - average molecular weight of 260000 , dissolved into the hexafluoro isopropyl alcohol . the hydrogel containing a cytokine adopts an alginate solution of hemostasis factor . the hemostasis factor has a concentration of 10 ppm in mass in the cytokine alginate solution . the solution with 0 . 1 m calcium chloride should be placed into the cell petri dish with a diameter of 150 mm . the co - receiver share by the spinning device and bio - printing is placed into the petri dish . in forming of an electrospun layer , the receiving device should contact with the solution in petri dish . the printer head is fixed below the electrospinning needle which is inside the spinning device box , which offers a function of fixed - point print on specific area with hemostasis factor . the prepared cytokine alginate solution is put into the cartridge of jet printer . in this embodiment , the cartridge is hp51626a . the hydrophobic electrospinning solution is placed into the sprayer for spinning . after that , adjust the velocity of micro - injection pump to be 5 milliliters / hour , the voltage of high voltage generator to be 30 kilovolts , and the receiving distance of receiving device to be 20 centimeters . the fiber is received in membrane structure . the spinning lasts for 20 minutes before the spinning device is closed . the hydrogel solution containing the cytokine is printed on the nano - bionic scaffold with jet printer . once the hydrogel is solidified , the hydrophobic electrospun layer with cytokine by bio - printing is acquired . an electrospinning solution , a hydrogel solution with medicine and the cross - linking agent solution are prepared . polyglycol and chondroitine sulfate , as hydrophilic materials , in the mass ratio of 70 : 30 are chosen . the spinning solution has the mass fraction of 9 %. the cross - linking agent solution is the 0 . 1m calcium chloride solution . the hydrogel solution containing a cytokine adopts the alginate solution with basic fibroblast factor . the basic alginate solution has the basic fibroblast factor at the concentration of 100 ppm . the parameters are set as follows : adjust the velocity of micro - injection pump to be 0 . 8 milliliters / hour , the voltage of high voltage generator to be 20 kilovolts and the receiving distance of receiving device to be 11 centimeters . other preparing procedures are the same as those in first step above . after the hydrophilic fiber is received in membrane structure , by bio - printing , the hydrogel solution containing the basic fibroblast factor is printed to the nano - bionic scaffold . once the hydrogel is solidified , the hydrophilic electrospun layer with cytokine by bio - printing is acquired . the rinse and store are the same as those in example 1 . ( 1 ) the preparation of hydrophobic electrospun layer with bio - printing is the same as described in example 6 . the electrospinning liquid solution of transition layer is comprises the polyurethane and the hyaluronic acid in the mass ratio of 70 : 30 . the mass fraction of the spinning solution is 10 %. the blended ampicillin is in the concentration of 3 %. the cross - linking agent solution is the 0 . 1 m calcium chloride solution . the hydrogel solution with cytokine is an alginate solution of hemostasis factor , and the mass percentage of the hemostasis factor is 10 ppm . the parameters are adjusted in this way as follows : the velocity of micro - injection pump is 4 milliliters / hour , the voltage of high voltage generator is 20 kilovolts , and the receiving distance is 11 centimeters . the other procedures are the same as the above procedures . the fiber is received in membrane structure . the hydrogel solution containing the cytokine will be printed on the transition layer . after the hydrogel is solidified , the hydrophobic electrospun layer with cytokine by bio - printing is obtained . ( 3 ) the preparation of hydrophilic electrospun layer with bio - printing is the same as described in example 6 . the rinse and store are the same as those described in example 1 . the dura mater obtained from example 1 is applied to dog for the animal experiment , while the control is a commercialized , clinical applicable heterogenic meninges repairing product . three healthy dogs are chosen , either male or female , in the weight between 10 and 15 kg , and under observation for two to three months . the dogs chosen in the experiment are under general anesthesia . their skulls are opened at both left and right sides . their dura maters are surgically removed , and the defects of dura maters and injuries of brain tissue appear . then , the dura maters obtained from the embodiment 1 and the control , respectively , are implanted for repairing the dural defects at the left and right sides of the dog &# 39 ; s brain . after operation , the dogs are feed normally as usual and observed periodically . the specimen is taken from the implanted area at the end of each observation period . in the end of the observation period , the skulls of the dogs are exposed by the way described above after general anesthesia . expose and separate the outer surface of the repairing material . to retrieve the samples , these dogs are sacrificed by administration of an intravenous injection of air . the skulls are opened surgically . the implants and surrounding tissue are taken out . the retrieved samples are inspected carefully with details including the appearance , characters , its relation to the surroundings cyst , callosity , as well as the adhesion between its inner surface and brain tissue . the specimen is stored in a bottle and treated and fixed with formalin solution . label the bottle . one week later , take out a local tissue ; embed with paraffin section and histological stain with he . several days after implantation , the three dogs recover well , and incisions are healed well with no obvious secretion . the dogs eat and drink normally as well as their outdoor activities are normal without any obvious movement malfunction . three months post - implantation , the three dogs are sacrifice by an intravenous injection of air . after sacrifice , taking the surgical site as center , the specimen is cut from one centimeter outer the operation site , and it includes the repair material , the surrounding dura mater and part of brain tissue . after the specimen is taken , separate the skull and meninges in order . it is found that the meninges , where dura mater transplanted , are formed completely ; the transplanted material has been replaced by fibrous tissue , and has connected tightly with the native meninges without border . the internal surface of the newly - formed meninges at transplantation site is free from adhesion with the brain tissue , and the surface of corresponding brain tissue is smooth and free from adhesion to the implant . while , in the implanted site of the control samples , the transplanted material has not yet degraded and exist a few of adhesion at the transplantation site to the internal surface of meninges . the dura mater prepared in the example 2 is now applied for the dog experiment . five dogs are in weight of 15 - 20 kg , 1 . 5 - 2 - year - old , and either male or female . they are in general anesthesia through the intramuscular injection of ketamine . after anesthesia and shave , the animals are placed on the operation table in lateroabdominal position . the disinfection is made with 2 % iodine and 75 % alcohol . the animals &# 39 ; heads are opened surgically in lengthwise direction . stripper is used to separate the periosteum of the skull , and the two top skull plateaus are exposed . the high - speed driller is used to open the skull . the two skull windows at vertex are formed , and two rectangular dura maters in size of 3 cm × 3 cm at the top of head are cut off with the scissors . finally the top dura mater defects are made for the following implantation with artificial dural mater and control . on the exposed brain surface , the electrocoagulation is applied to make 6 injury points in the size of 1 mm × 1 mm . then , the artificial dura mater manufactured in embodiment 2 is trimmed to the same shape and size as those of the dural defect and loaded into the defect . the hydrophobic layer is toward the brain surface , and the sutures is made with the 4 / 0 thread in the interval of 4 mm , to repair the dural defect of dogs . the round needle and 4 / 0 thread are used for suture of muscle . the commercialized , clinically applicable , animal material based dural repair product is applied as a control . after operation , the dogs are feed normally as usual and observed periodically . the animals recover well , and incisions are healed well . no obvious leakage of cerebrospinal fluid or occurrence of epilepsy is found . the dogs eat and drink normally as well as their outdoor activities are normal without any obvious movement malfunction , and they survive to the expected longevity . eighteen months post - implantation , the dogs are sacrificed and the specimen is taken at the surgical site , and it includes the artificial dura mater , the surrounding dura mater , and part of the surrounding brain tissue . after carefully observe the specimen , we can see that the connection between the artificial dura mater and native dura mater is tight and smooth , without clear boundary , healed well , besides , and with thread seen only . the native dura mater does not show any hyperaemia , hemorrhage or other rejection reaction . while , the results of the control show that the implant material is not yet degraded , and at the implanted site , the inner surface of meninges adheres to brain tissue to some degree . the artificial dura mater obtained from example 3 is now under the experiment with new zealand rabbit . the animals under experiment are opened in the skulls , and the defect of dura mater and injury of brain tissue are made surgically . then , the artificial dura mater is used to repair the defect . after the operation , the rabbits are feed normally as usual and observed periodically . these animals recover well . eighteen months post - implantation , the rabbits are sacrificed and the specimen is taken at the surgical site . the specimen includes the artificial dura mater , surrounding dura mater and part of the surrounding brain tissue . when observe the specimen carefully , it is seen that the epithelial cells cover the inner surface of the dura mater ; under the epithelium , fibrous tissue is formed , fibroblast progenitor cells proliferate , and collagen fibers are increased . all of these result in the formation of new vascularized tissues , in - growth of native dura mater , degradation of the implant material , deduction of total mass of the implant , and generation of rich capillary networks . in the interface of old and new tissues , no neutrophil , lymphocyte or other cell reaction for inflammation is found , and no cyst wall is formed . the arachnoid mater and brain tissue are normal . the dura mater obtained from example 4 is now applied to the dog experiment , and the method is the same as experimental example 2 . fifteen months post - implantation , the dogs are sacrificed and the specimen is taken at the surgical site . the specimen includes the artificial dura mater , surrounding dura mater , and part of the surrounding brain tissue . after carefully observe the specimen , it is seen that the connection between the artificial dura mater and native dura mater is tight and smooth , without clear boundary , completed cured , and with thread seen only . the native dura mater does not show hyperaemia , hemorrhage or other rejection reaction . the dura mater obtained from example 5 is now applied to the new zealand rabbit experiment , and the control is the commercialized , clinically applicable , animal materials based dura mater product as the repair material . the method is the same as experimental example 3 . fifteen months post - implantation , the rabbits are sacrificed and the specimen is taken at the surgical site . when observe the specimen carefully , it is seen that the epithelial cells cover the inner surface of the dura mater ; under the epithelium , fibrous tissue is formed , fibroblast progenitor cells proliferate , and collagen fibers are produced . all of these result in the formation of new vascularized tissues , in - growth of native dura mater , degradation of the implant material , deduction of total mass of the implant , and generation of rich capillary networks . in the interface of old and new tissues , no neutrophil , lymphocyte or other cell reaction for inflammation is found , and no cyst wall is formed . the arachnoid mater and brain tissue are normal . while , the results with the control show that the implant material is not yet degraded , and at the implanted site , the inner surface of meninges adheres to brain tissue to some degree . the dura mater obtained from example 6 is now applied to the dog experiment , and the method is the same as experimental example 2 . twelve months post - implantation , the dogs are sacrificed and the specimen is taken at the surgical site . the specimen includes the artificial dura mater , surrounding dura mater , and part of the surrounding brain tissue . when observe the specimen carefully , it is seen that the connection between the artificial dura mater and native dura mater is tight and smooth , without clear boundary , completed cured , and with thread seen only . the native dura mater does not show hyperaemia , hemorrhage or other rejection reaction . the dura mater obtained from example 7 is now applied to the new zealand rabbit experiment . the method is the same as experimental example 3 . twelve months post - implantation , the rabbits are sacrificed and the specimen is taken at the surgical site . when observe the specimen carefully , it is seen that the epithelial cells cover the inner surface of the dura mater ; under the epithelium fibrous tissue is formed , fibroblast progenitor cells proliferate , and collagen fibers are increase . all of these result in the formation of new vascularized tissues , in - growth of native dura mater , degradation of the implant material , deduction of total mass of the implant , and generation of rich capillary networks . in the interface of old and new tissues , no neutrophil , lymphocyte or other cell reaction of inflammation is found , and no cyst wall is formed . the arachnoid mater and brain tissue are normal . notwithstanding the embodiments have been given and described , the person skilled in the field can , without deviation from the principle and theory , can make the variation , modification , replacement and change of these embodiments , as given in the invention scope and right claims .