as 2 o 3 ( 0 . 30 g ) was milled into particles having an average particle size of 0 . 10 μm which were suspended in anhydrous alcohol ( 100 ml ), and surfactant span 80 ( 0 . 005 g ) was added thereto . polycaprolactone ( 2 . 5 g ) was dissolved in tetrahydrofuran solution ( 100 ml ), then the alcohol solution containing the arsenic trioxide particles was added to the polycaprolactone solution and dispersed therein under stirring , and then anhydrous alcohol ( 80 ml ) was added dropwise thereto under stirring to form a thin film of polycaprolactone on the surface of the as 2 o 3 particles , and a suspension was formed when the particles precipitated in a form of microcapsules . upon being sprayed uniformly with the suspension on the surface , the 316 stainless steel scaffold was dried in vacuum at 80 ° c . for 8 h to give the as 2 o 3 elution scaffold , wherein the content of as 2 o 3 was 0 . 05 μg / mm 2 and as 2 o 3 was fixed on the polymer coating in a form of “ isolated island ” structure , as indicated in fig2 . antibody cd133 was coated on the surface of the scaffold to adsorb endothelial progenitor cells in order to accelerate the repair of the endothelium . the release results were shown in fig3 . the above - mentioned as 2 o 3 medical elution scaffold was subjected to animal experiments , and the experimental method was as follows : three - month - old mini - pigs were used as the experimental samples . 20 mg / kg ketamine was injected intravenously to achieve general anesthesia , after disinfection and draping on the right - side groin , the femoral artery was separated and cut open , a 7f arterial sheath was placed therein , and 7f - guided ductal type coronary angiography was conducted ; a 0 . 014 ″ bmw guidewire was guided to the distal end of the coronary artery ( rca , lad , lcx ), and the scaffold was delivered along the guidewire , and then released with the expansion of balloon at certain pressure . after the balloon , the guidewire , the duct and the arterial sheath were removed , the groin was sutured . the animals were sacrificed after three months and hearts were harvested ; the scaffold was embedded in resin and then prepared as hard issue sections . after stained with hematoxylin and eosin respectively , the sections were photographed under a microscope and the area and thickness of the tunica intima were calculated . the results of the 3 - month animal experiment show that the thickness of the blood vessel tunica intima was 152 ± 41 μm , and the blood vessel sections were shown in fig4 and fig5 . no thrombus or hemangioma was observed . as 2 o 3 ( 1 . 0 g ) was milled into particles having an average particle size of 15 μm which were suspended in anhydrous alcohol ( 100 ml ), and surfactant span 80 ( 0 . 005 g ) was added thereto . poly ( lactide - co - glycolide ) ( 0 . 2 g , with the weight ratio of glycolide : lactide = 2 : 8 ) was dissolved in chloroform solution ( 100 ml ), then the alcohol solution containing the arsenic trioxide particles was added to the plga solution and dispersed therein under stirring , and then anhydrous alcohol ( 200 ml ) was added dropwise thereto under stirring to form a thin film of plga on the surface of the as 2 o 3 particles , and a suspension was formed when the particles precipitated in a form of microcapsules . upon being sprayed uniformly with the suspension on the surface , the nickel - cobalt alloy scaffold was dried in vacuum at 80 ° c . for 8 h to give the as 2 o 3 elution scaffold , wherein the content of as 2 o 3 was 2 . 65 μg / mm 2 and as 2 o 3 was fixed in the polymer coating in a form of “ isolated island ” structure . a polylactic acid sustained - release layer containing heparin was coated on the surface of the scaffold to prevent formation of acute thrombus and to control sustained - release of the medicine efficiently . the release results were shown in fig6 . the above - mentioned as 2 o 3 medical elution scaffold was subjected to animal experiments . the experimental results show that the thickness of the blood vessel tunica intima was 161 ± 38 μm , and the blood vessel sections were shown in fig7 and fig8 . no thrombus or hemangioma was observed . as 2 o 3 ( 1 . 0 g ) was milled into particles having an average particle size of 0 . 25 μm which were suspended in anhydrous alcohol ( 100 ml ), then surfactant tween 80 ( 0 . 0025 g ) was added thereto . polylactic acid ( 1 . 0 g ) was dissolved in a dichloromethane solution ( 100 ml ), then the alcohol solution containing the arsenic trioxide particles was added to the polylactic acid solution and dispersed therein under stirring , and then anhydrous alcohol ( 125 ml ) was added dropwise thereto under stirring to form a thin film of polylactic acid on the surface of the as 2 o 3 particles , and a suspension was formed when the particles precipitated in a form of microcapsules . upon being sprayed uniformly with the suspension on the surface , the 316 stainless steel scaffold was dried in vacuum at 80 ° c . for 8 h to give the as 2 o 3 elution scaffold , wherein the content of as 2 o 3 was 0 . 52 μg / mm 2 , the weight ratio of the medicine to the polymer was 1 : 1 , and as 2 o 3 was fixed in the polymer coating in a form of “ isolated island ” structure . the release results were shown in fig9 . the above - mentioned as 2 o 3 medical elution scaffold was subjected to animal experiments . the experimental results show that the thickness of the blood vessel tunica intima was 128 ± 25 μm , and the blood vessel sections were shown in fig1 and fig1 . no thrombus or hemangioma was observed . poly ( lactide - co - glycolide ) ( 1 g , weight ratio of glycolide : lactide = 1 : 1 ) copolymer was dissolved in a chloroform solution ( 100 ml ), and surfactant span 80 ( 0 . 098 g ) was added and mixed therewith to form an oil phase ; surfactant tween 80 ( 0 . 002 g ) was added to a saturated aqueous solution of as 2 o 3 ( 50 ml ) to form an aqueous phase . the aqueous phase was added to the oil phase and dispersed uniformly under stirring at 3000 rpm to form an emulsion . upon being sprayed with the emulsion on the surface , the scaffold was dried in vacuum at 75 ° c . for 10 h to form the as 2 o 3 elution scaffold , wherein the content of as 2 o 3 was 50 μg and as 2 o 3 was fixed in the polymer coating in a form of “ isolated island ” structure . antibody cd133 was coated on the surface of the scaffold to adsorb endothelial progenitor cells in order to accelerate the repair of the endothelium . the release results were shown in fig1 . the results of the 3 - month animal experiment show that the thickness of the blood vessel tunica intima was 143 ± 49 μm , and the blood vessel sections were shown in fig1 and fig1 . no thrombus or hemangioma was observed . polylactic acid ( 0 . 1 g ) was dissolved in a chloroform solution ( 100 ml ), and surfactant span 80 ( 0 . 098 g ) was added and mixed therewith to form an oil phase ; surfactant tween 80 ( 0 . 002 g ) was added to a saturated aqueous solution of as 2 o 3 ( 50 ml ) to form an aqueous phase . the aqueous phase was added to the oil phase and dispersed uniformly under stirring at 3000 rpm to form an emulsion . upon being sprayed with the emulsion on the surface , the scaffold was dried in vacuum at 75 ° c . for 10 h to form the as 2 o 3 elution scaffold , wherein the content of as 2 o 3 was 0 . 81 μg / mm 2 and as 2 o 3 was fixed in the polymer coating in a form of “ isolated island ” structure . antibody cd134 was coated on the surface of the scaffold to adsorb endothelial progenitor cells in order to accelerate the repair of the endothelium . the release results were shown in fig1 . the results of the 3 - month animal experiment show that the thickness of the blood vessel tunica intima was 143 ± 49 μm , and the blood vessel sections were shown in fig1 and fig1 . no thrombus or hemangioma was observed . polycaprolactone ( 0 . 1 g ) was dissolved in chloroform ( 100 ml ), and as 2 o 3 ( 1 . 0 g ) was dissolved in redistilled water ( 100 ml ). firstly the polymer solution was sprayed on the surface of the scaffold , and then the as 2 o 3 aqueous solution was sprayed thereon . upon drying , as 2 o 3 formed conglomerated particles on the surface of the scaffold , and a solvent was sprayed on the surface of the scaffold to level the polymer coating . enwrapping of the polymer was formed on the surface of the as 2 o 3 microparticles , and as 2 o 3 was fixed in the polymer coating in a form of “ isolated island ” structure , as indicated in fig1 . after drying , the polymer solution , the as 2 o 3 aqueous solution and the solvent were sprayed in this order until the medicine content achieved a desired amount . the content of as 2 o 3 was 1 . 25 μg / mm 2 . the release results were shown in fig1 . the results of the 3 - month animal experiment show that the thickness of the blood vessel tunica intima was 141 ± 44 μm , and the blood vessel sections were shown in fig2 and fig2 , no thrombus or hemangioma was observed . after 12 weeks of the scaffold implantation , no obvious hyperplasia can be observed in the blood vessel tunica intima , the area of cavity was increased distinctly , while not a single thrombus or hemangioma occurred ; the surface of the scaffold was fully covered by endothelium ; the tunica intima , tunica media and tunica adventitia of the blood vessel were clear , and no obvious inflammation was observed . the results were shown in fig2 and fig2 . 10 μm micropores were etched on the outer surface of the scaffold ( the surface of the scaffold in contact with blood vessels after being implanted in vivo ) with a laser etching machine . an emulsion was prepared with the method for preparing emulsion as described in example 1 , and the emulsion was distilled under reduced pressure to achieve a concentration of the microparticles of 30 % by weight . the solution was injected into the micropores , and after evaporation of the solvent , as 2 o 3 was fixed in the polymer coating in a form of “ isolated island ” structure on the outer surface of the scaffold , as indicated in fig2 . after drying in vacuum , the as 2 o 3 medical elution scaffold was obtained . the content of as 2 o 3 was 2 . 4 μg / mm 2 . the release results were shown in fig2 . the results of the 3 - month animal experiment show that the thickness of the blood vessel tunica intima was 128 ± 35 μm , and the blood vessel sections were shown in fig2 and fig2 with no thrombus or hemangioma observed inside the scaffold . the surface of the scaffold was fully covered by endothelium ; the tunica intima , tunica media and tunica adventitia of the blood vessel were clear , and no obvious inflammation was observed .
an arsenic trioxide medical elution scaffold and preparation method thereof , wherein the arsenic trioxide medical elution scaffold comprises scaffold , polymer coating covering the scaffold and arsenic trioxide loaded in the polymer coating which is in the form of single particle or particle conglomeration island . animal experiments testify that the medical release of the arsenic trioxide medical elution scaffold is suitably uniform , and can be controlled to meet clinic requirement .