TW201338817A - Biomedical implant material with composite antibacterium coating layer and manufacturing method thereof - Google Patents
Biomedical implant material with composite antibacterium coating layer and manufacturing method thereof Download PDFInfo
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- 239000002131 composite material Substances 0.000 title claims abstract description 56
- 239000007943 implant Substances 0.000 title claims abstract description 40
- 239000000463 material Substances 0.000 title claims abstract description 18
- 239000011247 coating layer Substances 0.000 title claims abstract 4
- 238000004519 manufacturing process Methods 0.000 title claims description 9
- 230000003115 biocidal effect Effects 0.000 claims abstract description 44
- 229920001222 biopolymer Polymers 0.000 claims abstract description 35
- 239000003242 anti bacterial agent Substances 0.000 claims abstract description 23
- 238000000151 deposition Methods 0.000 claims abstract description 20
- 239000003792 electrolyte Substances 0.000 claims abstract description 20
- 229940088710 antibiotic agent Drugs 0.000 claims abstract description 17
- 238000000034 method Methods 0.000 claims abstract description 17
- 230000008021 deposition Effects 0.000 claims abstract description 16
- 239000003929 acidic solution Substances 0.000 claims abstract description 5
- 238000004070 electrodeposition Methods 0.000 claims abstract description 4
- 238000000576 coating method Methods 0.000 claims description 59
- 239000011248 coating agent Substances 0.000 claims description 58
- 230000000844 anti-bacterial effect Effects 0.000 claims description 39
- 108010059993 Vancomycin Proteins 0.000 claims description 29
- 229960003165 vancomycin Drugs 0.000 claims description 29
- MYPYJXKWCTUITO-LYRMYLQWSA-N vancomycin Chemical compound O([C@@H]1[C@@H](O)[C@H](O)[C@@H](CO)O[C@H]1OC1=C2C=C3C=C1OC1=CC=C(C=C1Cl)[C@@H](O)[C@H](C(N[C@@H](CC(N)=O)C(=O)N[C@H]3C(=O)N[C@H]1C(=O)N[C@H](C(N[C@@H](C3=CC(O)=CC(O)=C3C=3C(O)=CC=C1C=3)C(O)=O)=O)[C@H](O)C1=CC=C(C(=C1)Cl)O2)=O)NC(=O)[C@@H](CC(C)C)NC)[C@H]1C[C@](C)(N)[C@H](O)[C@H](C)O1 MYPYJXKWCTUITO-LYRMYLQWSA-N 0.000 claims description 29
- MYPYJXKWCTUITO-UHFFFAOYSA-N vancomycin Natural products O1C(C(=C2)Cl)=CC=C2C(O)C(C(NC(C2=CC(O)=CC(O)=C2C=2C(O)=CC=C3C=2)C(O)=O)=O)NC(=O)C3NC(=O)C2NC(=O)C(CC(N)=O)NC(=O)C(NC(=O)C(CC(C)C)NC)C(O)C(C=C3Cl)=CC=C3OC3=CC2=CC1=C3OC1OC(CO)C(O)C(O)C1OC1CC(C)(N)C(O)C(C)O1 MYPYJXKWCTUITO-UHFFFAOYSA-N 0.000 claims description 29
- 229920001661 Chitosan Polymers 0.000 claims description 28
- QORWJWZARLRLPR-UHFFFAOYSA-H tricalcium bis(phosphate) Chemical compound [Ca+2].[Ca+2].[Ca+2].[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O QORWJWZARLRLPR-UHFFFAOYSA-H 0.000 claims description 25
- CEAZRRDELHUEMR-URQXQFDESA-N Gentamicin Chemical compound O1[C@H](C(C)NC)CC[C@@H](N)[C@H]1O[C@H]1[C@H](O)[C@@H](O[C@@H]2[C@@H]([C@@H](NC)[C@@](C)(O)CO2)O)[C@H](N)C[C@@H]1N CEAZRRDELHUEMR-URQXQFDESA-N 0.000 claims description 24
- 229930182566 Gentamicin Natural products 0.000 claims description 24
- 229960002518 gentamicin Drugs 0.000 claims description 24
- 108010010803 Gelatin Proteins 0.000 claims description 14
- 229920000159 gelatin Polymers 0.000 claims description 14
- 239000008273 gelatin Substances 0.000 claims description 14
- 235000019322 gelatine Nutrition 0.000 claims description 14
- 235000011852 gelatine desserts Nutrition 0.000 claims description 14
- 229910052751 metal Inorganic materials 0.000 claims description 14
- 239000002184 metal Substances 0.000 claims description 14
- 239000011575 calcium Substances 0.000 claims description 12
- 102000008186 Collagen Human genes 0.000 claims description 11
- 108010035532 Collagen Proteins 0.000 claims description 11
- 229920001436 collagen Polymers 0.000 claims description 11
- 229910052588 hydroxylapatite Inorganic materials 0.000 claims description 7
- HECLRDQVFMWTQS-UHFFFAOYSA-N Dicyclopentadiene Chemical compound C1C2C3CC=CC3C1C=C2 HECLRDQVFMWTQS-UHFFFAOYSA-N 0.000 claims description 6
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 claims description 6
- XYJRXVWERLGGKC-UHFFFAOYSA-D pentacalcium;hydroxide;triphosphate Chemical compound [OH-].[Ca+2].[Ca+2].[Ca+2].[Ca+2].[Ca+2].[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O XYJRXVWERLGGKC-UHFFFAOYSA-D 0.000 claims description 6
- 239000000243 solution Substances 0.000 claims description 6
- 239000010936 titanium Substances 0.000 claims description 6
- 229910052719 titanium Inorganic materials 0.000 claims description 6
- 229910001000 nickel titanium Inorganic materials 0.000 claims description 4
- 239000000203 mixture Substances 0.000 claims description 3
- 229910001220 stainless steel Inorganic materials 0.000 claims description 3
- 239000010935 stainless steel Substances 0.000 claims description 3
- 239000000602 vitallium Substances 0.000 claims description 2
- 229910000392 octacalcium phosphate Inorganic materials 0.000 claims 4
- YIGWVOWKHUSYER-UHFFFAOYSA-F tetracalcium;hydrogen phosphate;diphosphate Chemical compound [Ca+2].[Ca+2].[Ca+2].[Ca+2].OP([O-])([O-])=O.[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O YIGWVOWKHUSYER-UHFFFAOYSA-F 0.000 claims 4
- FUFJGUQYACFECW-UHFFFAOYSA-L calcium hydrogenphosphate Chemical compound [Ca+2].OP([O-])([O-])=O FUFJGUQYACFECW-UHFFFAOYSA-L 0.000 claims 2
- ZCCIPPOKBCJFDN-UHFFFAOYSA-N calcium nitrate Chemical compound [Ca+2].[O-][N+]([O-])=O.[O-][N+]([O-])=O ZCCIPPOKBCJFDN-UHFFFAOYSA-N 0.000 claims 2
- 235000019700 dicalcium phosphate Nutrition 0.000 claims 2
- HZEWFHLRYVTOIW-UHFFFAOYSA-N [Ti].[Ni] Chemical compound [Ti].[Ni] HZEWFHLRYVTOIW-UHFFFAOYSA-N 0.000 claims 1
- LFVGISIMTYGQHF-UHFFFAOYSA-N ammonium dihydrogen phosphate Chemical compound [NH4+].OP(O)([O-])=O LFVGISIMTYGQHF-UHFFFAOYSA-N 0.000 claims 1
- 229910000387 ammonium dihydrogen phosphate Inorganic materials 0.000 claims 1
- MYPYJXKWCTUITO-KIIOPKALSA-N chembl3301825 Chemical compound O([C@@H]1[C@@H](O)[C@H](O)[C@@H](CO)O[C@H]1OC1=C2C=C3C=C1OC1=CC=C(C=C1Cl)[C@@H](O)[C@H](C(N[C@@H](CC(N)=O)C(=O)N[C@H]3C(=O)N[C@H]1C(=O)N[C@H](C(N[C@H](C3=CC(O)=CC(O)=C3C=3C(O)=CC=C1C=3)C(O)=O)=O)[C@H](O)C1=CC=C(C(=C1)Cl)O2)=O)NC(=O)[C@@H](CC(C)C)NC)[C@H]1C[C@](C)(N)C(O)[C@H](C)O1 MYPYJXKWCTUITO-KIIOPKALSA-N 0.000 claims 1
- 235000019837 monoammonium phosphate Nutrition 0.000 claims 1
- 239000003814 drug Substances 0.000 abstract description 19
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- 229910021607 Silver chloride Inorganic materials 0.000 description 16
- 238000011068 loading method Methods 0.000 description 16
- HKZLPVFGJNLROG-UHFFFAOYSA-M silver monochloride Chemical compound [Cl-].[Ag+] HKZLPVFGJNLROG-UHFFFAOYSA-M 0.000 description 16
- 229910000389 calcium phosphate Inorganic materials 0.000 description 15
- 239000001506 calcium phosphate Substances 0.000 description 15
- 235000011010 calcium phosphates Nutrition 0.000 description 15
- QTBSBXVTEAMEQO-UHFFFAOYSA-N Acetic acid Chemical compound CC(O)=O QTBSBXVTEAMEQO-UHFFFAOYSA-N 0.000 description 9
- 238000003487 electrochemical reaction Methods 0.000 description 8
- 230000000399 orthopedic effect Effects 0.000 description 8
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- 238000007747 plating Methods 0.000 description 7
- 210000000988 bone and bone Anatomy 0.000 description 6
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- 238000000975 co-precipitation Methods 0.000 description 3
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- 210000000963 osteoblast Anatomy 0.000 description 3
- 238000011282 treatment Methods 0.000 description 3
- 229910000619 316 stainless steel Inorganic materials 0.000 description 2
- 241000894006 Bacteria Species 0.000 description 2
- 229910014497 Ca10(PO4)6(OH)2 Inorganic materials 0.000 description 2
- AOJJSUZBOXZQNB-TZSSRYMLSA-N Doxorubicin Chemical compound O([C@H]1C[C@@](O)(CC=2C(O)=C3C(=O)C=4C=CC=C(C=4C(=O)C3=C(O)C=21)OC)C(=O)CO)[C@H]1C[C@H](N)[C@H](O)[C@H](C)O1 AOJJSUZBOXZQNB-TZSSRYMLSA-N 0.000 description 2
- 238000005033 Fourier transform infrared spectroscopy Methods 0.000 description 2
- 206010061218 Inflammation Diseases 0.000 description 2
- 206010031252 Osteomyelitis Diseases 0.000 description 2
- 229910000883 Ti6Al4V Inorganic materials 0.000 description 2
- GWEVSGVZZGPLCZ-UHFFFAOYSA-N Titan oxide Chemical compound O=[Ti]=O GWEVSGVZZGPLCZ-UHFFFAOYSA-N 0.000 description 2
- 229910021529 ammonia Inorganic materials 0.000 description 2
- QGZKDVFQNNGYKY-UHFFFAOYSA-N ammonia Natural products N QGZKDVFQNNGYKY-UHFFFAOYSA-N 0.000 description 2
- 238000004458 analytical method Methods 0.000 description 2
- 229910052586 apatite Inorganic materials 0.000 description 2
- YYRMJZQKEFZXMX-UHFFFAOYSA-L calcium bis(dihydrogenphosphate) Chemical compound [Ca+2].OP(O)([O-])=O.OP(O)([O-])=O YYRMJZQKEFZXMX-UHFFFAOYSA-L 0.000 description 2
- 230000004663 cell proliferation Effects 0.000 description 2
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- 238000000445 field-emission scanning electron microscopy Methods 0.000 description 2
- 230000004054 inflammatory process Effects 0.000 description 2
- 150000002739 metals Chemical class 0.000 description 2
- VSIIXMUUUJUKCM-UHFFFAOYSA-D pentacalcium;fluoride;triphosphate Chemical compound [F-].[Ca+2].[Ca+2].[Ca+2].[Ca+2].[Ca+2].[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O VSIIXMUUUJUKCM-UHFFFAOYSA-D 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 239000002244 precipitate Substances 0.000 description 2
- 238000001356 surgical procedure Methods 0.000 description 2
- 229960000707 tobramycin Drugs 0.000 description 2
- NLVFBUXFDBBNBW-PBSUHMDJSA-N tobramycin Chemical compound N[C@@H]1C[C@H](O)[C@@H](CN)O[C@@H]1O[C@H]1[C@H](O)[C@@H](O[C@@H]2[C@@H]([C@@H](N)[C@H](O)[C@@H](CO)O2)O)[C@H](N)C[C@@H]1N NLVFBUXFDBBNBW-PBSUHMDJSA-N 0.000 description 2
- 102000002260 Alkaline Phosphatase Human genes 0.000 description 1
- 108020004774 Alkaline Phosphatase Proteins 0.000 description 1
- OYPRJOBELJOOCE-UHFFFAOYSA-N Calcium Chemical compound [Ca] OYPRJOBELJOOCE-UHFFFAOYSA-N 0.000 description 1
- 229920002101 Chitin Polymers 0.000 description 1
- MYMOFIZGZYHOMD-UHFFFAOYSA-N Dioxygen Chemical compound O=O MYMOFIZGZYHOMD-UHFFFAOYSA-N 0.000 description 1
- 241000588921 Enterobacteriaceae Species 0.000 description 1
- 241000192125 Firmicutes Species 0.000 description 1
- 241000233866 Fungi Species 0.000 description 1
- 238000004566 IR spectroscopy Methods 0.000 description 1
- 229910001182 Mo alloy Inorganic materials 0.000 description 1
- 241000283973 Oryctolagus cuniculus Species 0.000 description 1
- 102000004067 Osteocalcin Human genes 0.000 description 1
- 108090000573 Osteocalcin Proteins 0.000 description 1
- 229910010413 TiO 2 Inorganic materials 0.000 description 1
- 241000700605 Viruses Species 0.000 description 1
- 229940009456 adriamycin Drugs 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 230000003592 biomimetic effect Effects 0.000 description 1
- 229910052791 calcium Inorganic materials 0.000 description 1
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- 239000000499 gel Substances 0.000 description 1
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- 239000001257 hydrogen Substances 0.000 description 1
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- 239000001301 oxygen Substances 0.000 description 1
- 229910052760 oxygen Inorganic materials 0.000 description 1
- RFWLACFDYFIVMC-UHFFFAOYSA-D pentacalcium;[oxido(phosphonatooxy)phosphoryl] phosphate Chemical compound [Ca+2].[Ca+2].[Ca+2].[Ca+2].[Ca+2].[O-]P([O-])(=O)OP([O-])(=O)OP([O-])([O-])=O.[O-]P([O-])(=O)OP([O-])(=O)OP([O-])([O-])=O RFWLACFDYFIVMC-UHFFFAOYSA-D 0.000 description 1
- 230000003285 pharmacodynamic effect Effects 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
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- 229920001282 polysaccharide Polymers 0.000 description 1
- 239000005017 polysaccharide Substances 0.000 description 1
- 230000003449 preventive effect Effects 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
- 238000011321 prophylaxis Methods 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 238000003980 solgel method Methods 0.000 description 1
- 239000007921 spray Substances 0.000 description 1
- 230000001954 sterilising effect Effects 0.000 description 1
- 238000004659 sterilization and disinfection Methods 0.000 description 1
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- Materials For Medical Uses (AREA)
Abstract
Description
本發明係關於以電化學方法製備生物高分子/抗生素複合抗菌鍍層於生醫植入材。The invention relates to electrochemically preparing a biopolymer/antibiotic composite antibacterial coating on a biomedical implant.
任何骨科的相關手術都有感染骨隨炎的可能。所謂的骨髓炎係指骨組織遭微生物感染而引發一連串的發炎反應,進而破壞骨組織本體。致病微生物的種類有細菌、黴菌以及分支桿菌,甚至是病毒;其中以金黃色葡萄球菌(staphylococcus aureus)、腸道桿菌(enterobacteriaceae)、鏈球菌(streptococci)為最常見之感染源。若患者的體內具有骨科植入物(例如骨釘、骨板、人工關節等),菌種更易依附或聚集在該骨科植入物上,形成感染治療的難題。為解決此問題,一種將抗生素被覆於骨科植入物的方法被提出,期以抗生素與骨科植入物同步植入患者體內的方式,來達到修復骨組織及防止感染的目的。Any orthopedic related surgery has the potential to infect the bone with inflammation. The so-called osteomyelitis refers to a series of inflammatory reactions caused by microbial infection of bone tissue, thereby destroying the body of bone tissue. The type of pathogenic microorganisms are bacteria, fungi and mycobacteria, or even a virus; in which Staphylococcus aureus (staphylococcus aureus), intestinal bacteria (enterobacteriaceae), streptococci (streptococci) is the most common source of infection. If the patient has an orthopedic implant (such as a bone nail, a bone plate, an artificial joint, etc.) in the body, the strain is more likely to adhere or accumulate on the orthopedic implant, forming a problem of infection treatment. In order to solve this problem, a method of coating an antibiotic with an orthopedic implant has been proposed, in which the antibiotic and the orthopedic implant are implanted into the patient simultaneously to achieve the purpose of repairing the bone tissue and preventing infection.
關於抗生素被覆骨科植入物的文獻,如:Literature on antibiotic-coated orthopedic implants, such as:
文獻1:Volker Ait,Achim Bitschnau,Jana Osterling,Andreas Sewing,Christof Meyer,Ralf Kraus,Stefan A. Meissner,Sabine Wenisch,Eugen Domann,and Reinhard Schnettler,“The effects of combined gentamicin-hydroxyapatite coating for cementless joint prostheses on the reduction of infection rates in a rabbit infection prophylaxis model”,Biomaterials,27,4627~4634(2006)。Document 1: Volker Ait, Achim Bitschnau, Jana Osterling, Andreas Sewing, Christof Meyer, Ralf Kraus, Stefan A. Meissner, Sabine Wenisch, Eugen Domann, and Reinhard Schnettler, "The effects of combined gentamicin-hydroxyapatite coating for cementless joint prostheses on The reduction of infection rates in a rabbit infection prophylaxis model", Biomaterials, 27, 4627~4634 (2006).
文獻2: Peter J. Tarcha,Donald Verlee,Ho Wah Hui,Jeff Setesak,Bogdan Antone,Dellia Radulescu,and David Wallace,“The Application of Ink-Jet Techology for the Coating and Loading of Drug-Eluting Stents”,Annals of Biomedical Engineering,35,1793~1799(2007)。Document 2: Peter J. Tarcha, Donald Verlee, Ho Wah Hui, Jeff Setesak, Bogdan Antone, Dellia Radulescu, and David Wallace, “The Application of Ink-Jet Techology for the Coating and Loading of Drug-Eluting Stents”, Annals of Biomedical Engineering, 35, 1793~1799 (2007).
文獻3: M. Stigter,K. de Groot,and P. Layrolle,“Incorporation of tobramycin into biomimetic hydroxyapatite coating on titanium”,Biomaterials,23,4143~4153(2002)。Document 3: M. Stigter, K. de Groot, and P. Layrolle, "Incorporation of tobramycin into biomimetic hydroxyapatite coating on titanium", Biomaterials, 23, 4143-4153 (2002).
文獻4:Shula Radin,and Paul Ducheyne,“Controlled release of vancomycin from thin sol-gel films on titanium alloy fracture plate material”,Biomaterials,28,1721~1729(2007)。Document 4: Shula Radin, and Paul Ducheyne, "Controlled release of vancomycin from thin sol-gel films on titanium alloy fracture plate material", Biomaterials, 28, 1721 to 1729 (2007).
文獻5:陳逸安,“Vancomycin/磷酸鈣鹽複合塗層於已披覆生醫陶瓷Ti6Al4V植入材之研究”碩士論文(指導教授:顏秀崗),中興大學,2008。Document 5: Chen Yi'an, “Vancomycin/Calcium Phosphate Composite Coating on the Covered Biomedical Ceramic Ti6Al4V Implant Materials” Master's Thesis (Instructor: Yan Xiugang), Zhongxing University, 2008.
文獻6:林岑頤,“磷酸鈣鹽、明膠及健大黴素複合鍍層於已披覆HA/TiO2鈦金屬之特性研究”碩士論文(指導教授:顏秀崗),中興大學,2009。Document 6: Lin Biao, “Study on the Characteristics of Composite Coating of Calcium Phosphate, Gelatin and Jiandamycin on the Overlay of HA/TiO 2 Titanium” (Instructor: Yan Xiugang), Zhongxing University, 2009.
文獻7:羅俊譯,”沈積甲殼素/明膠/萬古黴素/磷酸鈣鹽複合鍍層於鈦合金之研究”碩士論文(指導教授:顏秀崗),中興大,2011。Document 7: Luo Jun translated, "Study on the deposition of chitin/gelatin/vancomycin/calcium phosphate composite coating on titanium alloy" (Professor: Yan Xiugang), Zhongxingda, 2011.
文獻1及文獻2,係利用噴墨技術(ink jet technology)將健大黴素(Gentamicin)噴塗於已被覆磷酸鈣鹽(HA)或磷酸鈣鹽-多肽複合物(HA-RGD)之不銹鋼基材上。抗生素載藥量為200~250μg/cm2,抗生素釋放持續時間15~20小時。此技術主要有兩個缺點,若基材的幾何形狀過於複雜,例如脊椎籠(Vertebral Body Cages),它包括各式幾何平面、粗糙面、曲率面、以及各種面與面的交角,這使噴塗技術的實施變得困難重重,不易噴塗均勻以,亦有局部無法噴塗的問題。此外,噴塗的抗生素只附著於基材的表面,一旦將基材植入人體後,抗生素即產生爆發性釋放(initial burst),藥效無法穩定維持一段時間。In Literature 1 and Document 2, Gentamicin was sprayed on a stainless steel base coated with calcium phosphate (HA) or calcium phosphate-polypeptide complex (HA-RGD) by ink jet technology. On the material. The antibiotic drug loading is 200~250μg/cm 2 , and the antibiotic release duration is 15~20 hours. This technique has two major drawbacks. If the geometry of the substrate is too complex, such as Vertebral Body Cages, it includes various geometric planes, rough surfaces, curvature surfaces, and various angles of intersection with the surface. The implementation of the technology has become difficult, it is not easy to spray evenly, and there is also the problem that it cannot be sprayed locally. In addition, the sprayed antibiotics only adhere to the surface of the substrate. Once the substrate is implanted into the human body, the antibiotics produce an initial burst, and the efficacy cannot be stably maintained for a period of time.
文獻3,係利用浸泡方式(immersion)將磷酸鈣鹽和托普黴素(Tobramycin)共沈於鈦合金基材上。此技術之缺點在於製程時間長,需花一天或一天以上的時間,而抗生素載藥量僅有5~10μg/cm2,抗生素釋放持續時間為50~60小時。Document 3 uses a immersion method to co-precipitate a calcium phosphate salt and a tobramycin on a titanium alloy substrate. The disadvantage of this technique is that the processing time is long and it takes a day or more, while the antibiotic drug loading is only 5~10μg/cm 2 and the antibiotic release duration is 50~60 hours.
文獻4,係利用溶膠凝膠法(sol-gel)將萬古黴素(Vancomycin)鍍於鈦合金基材上。抗生素載藥量為35~50μg/cm2,抗生素釋放持續時間為3~4天。其缺點是製作成本高,對於幾何形狀過於複雜的基材有鍍層不均勻及藥物濃度分布不均的問題。In Document 4, vancomycin was plated on a titanium alloy substrate by a sol-gel method. The antibiotic drug loading is 35~50μg/cm 2 , and the antibiotic release duration is 3~4 days. The disadvantage is that the manufacturing cost is high, and the substrate having an excessively complicated geometric shape has a problem of uneven plating and uneven distribution of drug concentration.
文獻5,係將萬古黴素(Vancomycin)與磷酸鈣鹽複合塗層(vancomycin-CaP)進一步塗佈於已具生醫陶瓷鍍層之Ti6Al4V合金上。抗生素載藥量為26.6 μg/cm2,抗生素釋放持續時間約24小時。In Document 5, vancomycin and calcium phosphate composite coating (vancomycin-CaP) was further coated on Ti6Al4V alloy which has been coated with biomedical ceramics. The antibiotic drug loading was 26.6 μg/cm2 and the antibiotic release lasted approximately 24 hours.
文獻6,係以電化學方式將明膠、健大黴素及磷酸鈣鹽共鍍於氫氧基磷灰石/二氧化鈦的雙層鍍膜上。抗生素載藥量為46~94μg/cm2。Document 6, electrochemically plating gelatin, gentamicin and calcium phosphate on a two-layer coating of hydroxyapatite/titanium dioxide. The antibiotic drug loading was 46~94μg/cm2.
本發明之目的係在提供一種具有複合抗菌鍍層之生醫植入材,所述之生醫植入材係可導電醫療用金屬,該生醫植入材的表面具有生物高分子及抗生素複合抗菌鍍層,該複合抗菌鍍層具有高單位面積的抗生素載藥量(可高達543μg/cm2),抗生素的釋放最長可達30天。且因生物高分子之附加,提昇了細胞貼附率及細胞增值、分化功能。與先前技術文獻相較,本發明之抗生素載藥量、抗生素穩定釋放、釋放持續時間、以及組織細胞恢復等各方面均有顯著提昇。The object of the present invention is to provide a biomedical implant material having a composite antibacterial coating, wherein the biomedical implant is a conductive medical metal, and the surface of the biomedical implant has a biopolymer and an antibiotic composite antibacterial. The coating has a high unit area of antibiotic drug loading (up to 543 μg/cm 2 ) and antibiotic release for up to 30 days. Moreover, due to the addition of biopolymers, cell attachment rate, cell proliferation and differentiation function are enhanced. Compared with the prior art literature, the antibiotic drug loading amount, stable release of antibiotics, duration of release, and recovery of tissue cells of the present invention are significantly improved.
本發明之目的係在提供一種製備生物高分子/抗生素複合抗菌鍍層於生醫植入材的方法,該方法具體的提昇了單位面積的抗生素載藥量,並延長了抗生素的釋放時間。此外,以本發明方法所製出之生醫植入材亦具有顯著的細胞貼附率、增值和分化。The object of the present invention is to provide a method for preparing a biopolymer/antibiotic composite antibacterial coating on a biomedical implant material, which specifically increases the antibiotic drug loading per unit area and prolongs the release time of the antibiotic. In addition, the biomedical implants produced by the method of the present invention also have significant cell attachment rates, proliferation, and differentiation.
本發明之目的係在提供一種製備生物高分子/抗生素複合抗菌鍍層於生醫植入材的方法,該方法係以電化學技術將生物高分子及抗生素共沈於可導電金屬植入材。生醫植入材的幾何形狀不會使電化學鍍層沈積受到限制,本發明可以實現在任何幾何形狀的生醫植入材上,全面性的在生醫植入材鍍上均勻的複合抗菌鍍層。The object of the present invention is to provide a method for preparing a biopolymer/antibiotic composite antibacterial coating on a biomedical implant material, which is an electrochemical technique for co-precipitating a biopolymer and an antibiotic onto a conductive metal implant. The geometry of the biomedical implant does not limit the deposition of the electrochemical coating. The present invention can realize a comprehensive composite antibacterial coating on the biomedical implant plating on the biomedical implant of any geometric shape. .
本發明達成上述目的之技術:The technology of the present invention to achieve the above object:
在一三極電化學系統中,以具導電性之金屬生醫植入材為工作電極,以混合生物高分子和抗生素之酸性溶液做為該三極電化學系統之電解液,電解液溫度為25℃至75℃之間的一個固定值;以相對於該三極電化學系統之參考電極設定一恆定電位,該恆定電位為介於-0.5~-3.0伏特之間的一個固定值;據此進行電化學沈積,於該生醫植入材的表面形成一生物高分子與抗生素複合抗菌鍍層;將完成複合抗菌鍍層沈積的工作電極取出,於25℃陰乾。In a three-electrode electrochemical system, a conductive metal biomedical implant is used as a working electrode, and an acidic solution of a mixed biopolymer and an antibiotic is used as an electrolyte of the three-electrode electrochemical system, and the electrolyte temperature is a fixed value between 25 ° C and 75 ° C; a constant potential is set relative to a reference electrode of the three-electrode electrochemical system, the constant potential being a fixed value between -0.5 and -3.0 volts; Electrochemical deposition is performed to form a bio-polymer and antibiotic composite antibacterial coating on the surface of the biomedical implant; the working electrode for performing the composite antibacterial plating deposition is taken out and dried at 25 ° C.
本發明電化學沈積生物高分子/抗生素複合抗菌鍍層於生醫植入材的方法,係以三極電化學系統實現。如第一圖,該電化學系統包括一參考電極20;一輔助電極30;一工作電極50;一供電單元10與上各電極耦合;一操作單元70與上述供電單元70耦合;一容器40盛裝電解液60,上述各電極置入該電解液60中。所述之電解液主要含有抗生素及生物高分子。該操作單元70包括一恆電位/電流儀80(Potentiostat Galvanostat)與一電腦90,而該電腦90與該恆電位/電流儀80連結設置,以讓該操作單元70經由該供電單元10而對該參考電極20、輔助電極30、工作電極50進行導電操作。該輔助電極30為白金。該參考電極20為銀/氯化銀(Ag/AgCl),相對該參考電極該導電電位最佳範圍值為-0.5~-3.0伏特之間的一個固定值。恆電位掃描率約為0.167mV/sec。操作時間為600 sec。該工作電極50為可導電之醫療植入用金屬基材,直徑為14 mm,厚度為1.0 mm。操作溫度為25℃至75℃之間的一個固定值。The method for electrochemically depositing a biopolymer/antibiotic composite antibacterial coating on a biomedical implant is realized by a three-electrode electrochemical system. As shown in the first figure, the electrochemical system includes a reference electrode 20, an auxiliary electrode 30, a working electrode 50, a power supply unit 10 coupled to the upper electrodes, an operating unit 70 coupled to the power supply unit 70, and a container 40. In the electrolytic solution 60, each of the above electrodes is placed in the electrolytic solution 60. The electrolyte mainly contains antibiotics and biopolymers. The operating unit 70 includes a potentiostat Galvanostat and a computer 90, and the computer 90 is coupled to the potentiostat/current meter 80 to allow the operating unit 70 to pass the power unit 10 via the power unit 10. The reference electrode 20, the auxiliary electrode 30, and the working electrode 50 perform a conductive operation. The auxiliary electrode 30 is platinum. The reference electrode 20 is silver/silver chloride (Ag/AgCl), and the conductive potential is optimally set to a fixed value between -0.5 and -3.0 volts with respect to the reference electrode. The potentiostatic scan rate is approximately 0.167 mV/sec. The operating time is 600 sec. The working electrode 50 is an electrically conductive metal substrate for medical implantation having a diameter of 14 mm and a thickness of 1.0 mm. The operating temperature is a fixed value between 25 ° C and 75 ° C.
啟動電化學系統,在工作電極50的表面形成生物高分子/抗生素鍍層。The electrochemical system is activated to form a biopolymer/antibiotic coating on the surface of the working electrode 50.
之後,將工作電極從電解液中取出,在25℃環境下陰乾,即完成製備。Thereafter, the working electrode was taken out from the electrolytic solution and dried in an environment of 25 ° C to complete the preparation.
關於複合抗菌鍍層之特徵,本發明分別利用X光繞射儀(XRD)、場發射掃描式電子顯微鏡(FESEM/EDS)、傅立葉紅外線光譜(FTIR)、穿透式電子顯微鏡(Transmission Electron Microscopy:TEM)進行分析。Regarding the characteristics of the composite antibacterial coating, the present invention utilizes an X-ray diffractometer (XRD), a field emission scanning electron microscope (FESEM/EDS), a Fourier infrared spectroscopy (FTIR), and a transmission electron microscope (Transmission Electron Microscopy: TEM), respectively. ) for analysis.
關於複合抗菌鍍層之含藥量以及藥物釋放,本發明分光光度計(UV visible spectrometer)進行分析。Regarding the drug content of the composite antibacterial coating and drug release, the present invention is analyzed by a UV visible spectrometer.
關於複合抗菌鍍層之抗菌試驗,本發明主要量測金黃色葡萄球菌的活菌數,並以抑菌圈試驗進行分析。Regarding the antibacterial test of the composite antibacterial coating, the present invention mainly measures the viable count of Staphylococcus aureus and analyzes it by the inhibition zone test.
最後再以細胞培養、細胞增殖(MTT)、鹼性磷酸酶活性(ALP)及骨鈣素(osteocalcin)檢測成骨細胞在試片上貼附、增殖、分化與礦化之情形。Finally, cell culture, cell proliferation (MTT), alkaline phosphatase activity (ALP) and osteocalcin were used to detect the attachment, proliferation, differentiation and mineralization of osteoblasts on the test pieces.
實施例一採用上述電化學系統,電解液為混合2wt%幾丁聚醣及10mg/ml健大黴素溶於0.0033 vol%乙酸溶液,固定電壓為-1.0V,操作溫度60℃。工作電極採用經研磨清洗之醫療用316不鏽鋼。啟動上述電化學系統,幾丁聚醣及健大黴素於工作電極上產生陰極沉積反應,形成一幾丁聚醣/健大黴素複合抗菌鍍層。完成陰極沉積反應後,將工作電極由電解液中取出,經25℃陰乾後完成製備。In the first embodiment, the above electrochemical system was used. The electrolyte was mixed with 2 wt% chitosan and 10 mg/ml gentamicin dissolved in 0.0033 vol% acetic acid solution at a fixed voltage of -1.0 V and an operating temperature of 60 °C. The working electrode is a medically cleaned 316 stainless steel. Starting the above electrochemical system, chitosan and gentamicin produce a cathodic deposition reaction on the working electrode to form a chitosan/gentamicin composite antibacterial coating. After the cathode deposition reaction is completed, the working electrode is taken out from the electrolyte, and the preparation is completed after drying at 25 ° C.
第二圖為實施例一幾丁聚醣與健大黴素複合鍍層極化曲線圖,可見到一反應曲線120,以及幾丁聚醣與健大黴素複合鍍層反應區130。The second figure is a polarization curve of the composite coating of chitosan and gentamicin in the first embodiment, and a reaction curve 120 and a reaction zone 130 of chitosan and gentamicin composite plating are seen.
4H++O2+4e-→2H2O E0=0.5~-0.25V vs. Ag/AgCl4H + +O 2 +4e - →2H 2 O E 0 =0.5~-0.25V vs. Ag/AgCl
2H++2e-→H2 E0=-0.25~-0.75V vs. Ag/AgCl2H + +2e - →H 2 E 0 =-0.25~-0.75V vs. Ag/AgCl
2H2O+2e-→H2+2OH- E0=-0.75~-3.0V vs. Ag/AgCl2H 2 O+2e - →H 2 +2OH - E 0 =-0.75~-3.0V vs. Ag/AgCl
Chitosan-NH3 + (1)+OH-→Chitosan-NH2(↓)+H2OChitosan-NH 3 + (1) +OH - →Chitosan-NH 2(↓) +H 2 O
由以上電化學反應可知,在沉積幾丁聚醣的過程中健大黴素含有氨鍵可與幾丁聚醣結合而共沉於醫療用不鏽鋼上,進而得到最佳條件的幾丁聚醣與健大黴素複合抗菌鍍層,其電子顯微鏡觀察圖如第六圖。該抗菌鍍層的厚度約為3.6 μm,健大黴素載藥量為204.16μg/cm2,抑菌圈直徑d(mm)為32;藥效釋放時間可維持28天;在細胞培養實驗中顯示,骨細胞確能貼附、增殖、分化、及礦化。It can be seen from the above electrochemical reaction that during the deposition of chitosan, the gentamicin contains an amino bond which can be combined with chitosan to coprecipitate on the medical stainless steel, thereby obtaining the optimal condition of chitosan and The electromycin microscopic observation of the gentamicin composite antibacterial coating is as shown in the sixth figure. The antibacterial coating has a thickness of about 3.6 μm, the gentamicin has a drug loading of 204.16 μg/cm 2 , the inhibition zone diameter d (mm) is 32, and the pharmacodynamic release time can be maintained for 28 days; Osteoblasts can indeed attach, proliferate, differentiate, and mineralize.
實施例二採用上述電化學系統,電解液為混合2wt%幾丁聚醣及10mg/ml萬古黴素溶於0.0033 vol%乙酸溶液,固定電壓為-1.0V,操作溫度60℃。工作電極採用經研磨清洗之醫療用CCM合金。啟動上述電化學系統,幾丁聚醣及萬古黴素於工作電極上產生陰極沉積反應,形成一幾丁聚醣/萬古黴素複合抗菌鍍層。完成陰極沉積反應後,將工作電極由電解液中取出,經25℃陰乾後完成製備。In the second embodiment, the above electrochemical system is used. The electrolyte is mixed with 2 wt% chitosan and 10 mg/ml vancomycin dissolved in 0.0033 vol% acetic acid solution, the fixed voltage is -1.0 V, and the operating temperature is 60 °C. The working electrode is a medically cleaned CCM alloy. Starting the above electrochemical system, chitosan and vancomycin produce a cathodic deposition reaction on the working electrode to form a chitosan/vancomycin composite antibacterial coating. After the cathode deposition reaction is completed, the working electrode is taken out from the electrolyte, and the preparation is completed after drying at 25 ° C.
第三圖為實施例二幾丁聚醣與萬古黴素複合鍍層極化曲線圖,可見到一反應曲線140,及幾丁聚醣及萬古黴素複合鍍層反應區150。其可能發生的電化學反應如下:The third figure is the polarization curve of the composite coating of chitosan and vancomycin in the second embodiment, and a reaction curve 140 and a reaction zone 150 of chitosan and vancomycin composite plating are seen. The electrochemical reactions that may occur are as follows:
4H++O2+4e-→2H2O E0=0.5~-0.2V vs. Ag/AgCl4H + +O 2 +4e - →2H 2 O E 0 =0.5~-0.2V vs. Ag/AgCl
2H++2e-→H2 E0=-0.2~-0.9V vs. Ag/AgCl2H + +2e - →H 2 E 0 =-0.2~-0.9V vs. Ag/AgCl
2H2O+2e-→H2+2OH- E0=-0.9~-3.0V vs. Ag/AgCl2H 2 O+2e - →H 2 +2OH - E 0 =-0.9~-3.0V vs. Ag/AgCl
Chitosan-NH3 + (1)+OH-→Chitosan-NH2(↓)+H2OChitosan-NH 3 + (1) +OH - →Chitosan-NH 2(↓) +H 2 O
由以上電化學反應可知,在沉積幾丁聚醣的過程中萬古黴素含有氨鍵可與幾丁聚醣結合而共沉於醫療用CCM合金上,進而得到最佳條件的幾丁聚醣/萬古黴素複合抗菌鍍層,其電子顯微鏡觀察圖如第七圖。該抗菌鍍層的厚度約為3.6 μm,健大黴素載藥量為543.42μg/cm2,抑菌圈直徑d(mm)為32。藥效釋放時間可維持30天;在細胞培養實驗中顯示,骨細胞確能貼附、增殖、分化、及礦化。It can be seen from the above electrochemical reaction that in the process of depositing chitosan, vancomycin contains an amino bond and can be combined with chitosan to coprecipitate on the CCM alloy for medical use, thereby obtaining optimal conditions of chitosan/ The vancomycin composite antibacterial coating has an electron microscope observation chart as shown in the seventh figure. The antibacterial coating has a thickness of about 3.6 μm, the gentamicin has a drug loading of 543.42 μg/cm 2 , and the inhibition zone diameter d (mm) is 32. The release time of the drug can be maintained for 30 days; in the cell culture experiment, the bone cells can be attached, proliferated, differentiated, and mineralized.
實施例三採用上述電化學系統,電解液為混合磷酸鈣鹽(0.042M Ca(NO3)2‧4H2O和0.025M NH4H2PO4)、0.3wt%明膠及10 mg/ml健大黴素於乙酸溶液,固定電壓為-1.0V,操作溫度60℃。工作電極採用經研磨清洗之醫療用鈦金屬。啟動上述電化學系統,明膠、磷酸鈣鹽與健大黴素於工作電極上產生陰極沉積反應,形成一明膠/磷酸鈣鹽/健大黴素複合抗菌鍍層。完成陰極沉積反應後,將工作電極由電解液中取出,經25℃陰乾後完成製備。The third embodiment adopts the above electrochemical system, the electrolyte is mixed calcium phosphate salt (0.042M Ca(NO 3 ) 2 ‧4H 2 O and 0.025M NH 4 H 2 PO 4 ), 0.3wt% gelatin and 10 mg/ml The adriamycin is in acetic acid solution, the fixed voltage is -1.0V, and the operating temperature is 60 °C. The working electrode is a medically-used titanium metal that has been ground and cleaned. Starting the above electrochemical system, gelatin, calcium phosphate and Jiandamycin produce a cathodic deposition reaction on the working electrode to form a gelatin/calcium phosphate/gentamicin composite antibacterial coating. After the cathode deposition reaction is completed, the working electrode is taken out from the electrolyte, and the preparation is completed after drying at 25 ° C.
第四圖為實施例三明膠、磷酸鈣鹽、健大黴素複合鍍層極化曲線圖,可見到一反應曲線100,及磷酸鈣鹽與明膠、健大黴素複合鍍層反應區110。其可能發生的電化學反應如下:The fourth figure is a polarization curve of the composite coating of gelatin, calcium phosphate and gentamicin in the third embodiment. A reaction curve 100 and a reaction zone 110 of a composite coating of calcium phosphate and gelatin and gentamicin are visible. The electrochemical reactions that may occur are as follows:
O2+2H2O+4e-→4OH- E0=0~-0.5V vs. Ag/AgClO 2 +2H 2 O+4e - →4OH - E 0 =0~-0.5V vs. Ag/AgCl
2H++2e-→H2 E0=-0.5~-1.0V vs. Ag/AgCl2H + +2e - →H 2 E 0 =-0.5~-1.0V vs. Ag/AgCl
2H2PO4-+2e-→2HPO4 2-+H2 E0=-1.0~-1.6V vs. Ag/AgCl2H 2 PO 4- +2e - →2HPO 4 2- +H 2 E 0 =-1.0~-1.6V vs. Ag/AgCl
H2PO4 -+2e-→PO4 3-+H2 H 2 PO 4 - +2e - →PO 4 3- +H 2
2H2O+2e-→H2+2OH- E0=-1.6~-3.0V vs. Ag/AgCl2H 2 O+2e - →H 2 +2OH - E 0 =-1.6~-3.0V vs. Ag/AgCl
Ca2++HPO4 2-+2H2O→CaHPO4‧2H2O(DCPD)Ca 2+ +HPO 4 2- +2H 2 O→CaHPO 4 ‧2H 2 O(DCPD)
8Ca2++8HPO4 2-+5H2O→Ca8H2(PO4)6‧5H2O+2H3PO4(OCP)8Ca 2+ +8HPO 4 2- +5H 2 O→Ca 8 H 2 (PO 4 ) 6 ‧5H 2 O+2H 3 PO 4 (OCP)
8Ca2++2HPO4 2-+4PO4 3-+5H2O→Ca8H2(PO4)6‧5H2O(OCP)8Ca 2+ +2HPO 4 2- +4PO 4 3- +5H 2 O→Ca 8 H 2 (PO 4 ) 6 ‧5H 2 O(OCP)
10Ca2++6PO4 3-+2OH-→Ca10(PO4)6(OH)2(HA)10Ca 2+ +6PO 4 3- +2OH - →Ca 10 (PO 4 ) 6 (OH) 2 (HA)
由以上電化學反應可知,在沉積DCPD、OCP、HA等磷酸酸鈣鹽的過程中,因為在水溶液健大黴素、明膠以及Ca2+和H2PO4-之間可藉由氨鍵作用而形成錯離子共沉於醫療用鈦金屬,進而得到最佳條件的明膠/氫氧機磷灰石/健大黴素複合鍍層。該抗菌鍍層的健大黴素載藥量為106.34 μg/cm2,抑菌圈直徑d(mm)為35;藥效釋放時間維持28天;在細胞培養實驗中顯示,骨細胞確能貼附、增殖、分化、及礦化。It can be seen from the above electrochemical reaction that in the process of depositing calcium phosphate phosphate such as DCPD, OCP, HA, etc., because of the ammonia bond between the aqueous solution of gentamicin, gelatin, and Ca 2+ and H 2 PO 4- The gelatin/oxygen machine apatite/gentamicin composite coating is formed by forming the wrong ions in the titanium metal for medical treatment. The antibacterial coating has a drug-loading amount of 106.34 μg/cm 2 , a diameter of d (mm) of 35, and a release time of 28 days; in cell culture experiments, bone cells can be attached. , proliferation, differentiation, and mineralization.
實施例四採用上述電化學系統,電解液為混合磷酸鈣鹽(0.042M Ca(NO3)2‧4H2O和0.025M NH4H2PO4)、0.025%膠原蛋白及10 mg/ml萬古黴素於水溶液,操作溫度60℃。工作電極採用經研磨清洗之醫療用鎳鈦合金。啟動上述電化學系統,膠原蛋白、磷酸鈣鹽與萬古黴素於工作電極上產生陰極沉積反應,形成一膠原蛋白/磷酸鈣鹽/萬古黴素複合抗菌鍍層。完成陰極沉積反應後,將工作電極由電解液中取出,經25℃陰乾後完成製備。Embodiment 4 uses the above electrochemical system, the electrolyte is mixed calcium phosphate salt (0.042M Ca(NO 3 ) 2 ‧4H 2 O and 0.025M NH 4 H 2 PO 4 ), 0.025% collagen and 10 mg/ml Wangu The solution was in aqueous solution at an operating temperature of 60 °C. The working electrode is a medical nickel-titanium alloy that has been ground and cleaned. Starting the above electrochemical system, collagen, calcium phosphate and vancomycin produce a cathodic deposition reaction on the working electrode to form a collagen/calcium phosphate/vancomycin composite antibacterial coating. After the cathode deposition reaction is completed, the working electrode is taken out from the electrolyte, and the preparation is completed after drying at 25 ° C.
第五圖為實施例四膠原蛋白、磷酸鈣鹽、萬古黴素複合鍍層極化曲線圖,可見到一反應曲線160,以及磷酸鈣鹽與膠原蛋白、萬古黴素複合鍍層反應區170。其可能發生的電化學反應如下:The fifth figure is a polarization curve of the composite coating of collagen, calcium phosphate and vancomycin in the fourth embodiment. A reaction curve 160 and a reaction zone 170 of a composite coating of calcium phosphate with collagen and vancomycin are visible. The electrochemical reactions that may occur are as follows:
O2+2H2O+4e-→4OH- E0=0~-0.5V vs. Ag/AgClO 2 +2H 2 O+4e-→4OH - E 0 =0~-0.5V vs. Ag/AgCl
2H++2e-→H2 E0=-0.5~-1.0V vs. Ag/AgCl 2H + +2e-→H 2 E 0 =-0.5~-1.0V vs. Ag/AgCl
2H2PO4-+2e-→2HPO4 2-+H2 E0=-1.0~-1.6V vs. Ag/AgCl 2H 2 PO 4- +2e - →2HPO 4 2- +H 2 E 0 =-1.0~-1.6V vs. Ag/AgCl
H2PO4 -+2 -→PO4 3-+H2 H 2 PO 4 - + 2 - →PO 4 3- +H 2
2H2O+2e-→H2+2OH-E0=-1.6~-3.0V vs. Ag/AgCl2H 2 O+2e - →H 2 +2OH - E 0 =-1.6~-3.0V vs. Ag/AgCl
Ca2++HPO4 2-+2H2O→CaHPO4‧2H2O(DCPD)Ca 2+ +HPO 4 2- +2H 2 O→CaHPO 4 ‧2H 2 O(DCPD)
8Ca2++8HPO4 2-+5H2O→Ca8H2(PO4)6‧5H2O+2H3PO4(OCP)8Ca 2+ +8HPO 4 2- +5H 2 O→Ca 8 H 2 (PO 4 ) 6 ‧5H 2 O+2H 3 PO 4 (OCP)
8Ca2++2HPO4 2-+4PO4 3-+5H2O→Ca8H2(PO4)6‧5H2O(OCP)8Ca 2+ +2HPO 4 2- +4PO 4 3- +5H 2 O→Ca 8 H 2 (PO 4 ) 6 ‧5H 2 O(OCP)
10Ca2++6PO4 3-+2OH-→Ca10(PO4)6(OH)2(HA)10Ca 2+ +6PO 4 3- +2OH - →Ca 10 (PO 4 ) 6 (OH) 2 (HA)
由以上電化學反應可知,在沉積DCPD、OCP、HA等磷酸酸鈣鹽的過程中,因為在水溶液、萬古黴素、膠原蛋白以及Ca2+和H2PO4-之間可藉由氨鍵作用而形成錯離子共沉於導電基材,進而得到最佳條件的氫氧機磷灰石/膠原蛋白/萬古黴素複合鍍層。該抗菌鍍層的健大黴素載藥量為174.5 μg/cm2,抑菌圈直徑d(mm)為35。藥效釋放時間維持28天;在細胞培養實驗中顯示,骨細胞確能貼附、增殖、分化、及礦化。It can be seen from the above electrochemical reaction that in the process of depositing calcium phosphate phosphate such as DCPD, OCP, HA, etc., because of the ammonia bond between aqueous solution, vancomycin, collagen, and Ca 2+ and H 2 PO 4- The effect is to form a counter electrode to co-precipitate on the conductive substrate, thereby obtaining an optimum condition of the oxyhydrogen machine apatite/collagen/vancomycin composite coating. The antibacterial coating had a statin-loading amount of 174.5 μg/cm 2 and a zone diameter d (mm) of 35. The release time of the drug was maintained for 28 days; in the cell culture experiment, the bone cells were indeed attached, proliferated, differentiated, and mineralized.
本發明將生物高分子及抗生素透過電化學技術沉積在醫療用金屬植入物上。已知抗生素無法藉由電化學方式單獨沉積,但卻可藉由與生物高分子形成氫鍵並在電化學過程中將生物高分子去質子化(deprotonation)而共沉形成生物高分子/抗生素複合鍍層。The invention deposits biopolymers and antibiotics on medical metal implants by electrochemical techniques. It is known that antibiotics cannot be deposited by electrochemical means alone, but can form a biopolymer/antibiotic complex by forming a hydrogen bond with a biopolymer and deprotonating the biopolymer in an electrochemical process. Plating.
藉由XRD、TEM、FESEM、FTIR以及UV/Vis分析,結果顯示,電化學沉積的生物高分子薄膜是由奈米級纖維所構成,抗生素加入時因pH值降低使得生物高分子纖維直徑縮減,抗生素分子插嵌在生物高分子纖維之間,顯然,抗生素可以很容易的與生物高分子鍵合而共沈於醫療用金屬材。The results of XRD, TEM, FESEM, FTIR and UV/Vis analysis show that the biodeposited biopolymer film is composed of nanofibers. When the antibiotics are added, the diameter of the biopolymer fibers is reduced due to the decrease of pH. Molecules are intercalated between biopolymer fibers. Obviously, antibiotics can easily bond with biopolymers and sink in medical metal.
生物高分子/抗生素複合鍍層中,抗生素的載藥量可藉由沉積時間和電位來控制。本發明採用的外加電壓範圍為-0.5~-3.0伏特,當外加電壓增加,抗生素的載藥量亦增加,其範圍從150到550 μg/cm2。In biopolymer/antibiotic composite coatings, the drug loading of antibiotics can be controlled by deposition time and potential. The applied voltage range of the present invention is -0.5 to -3.0 volts. When the applied voltage is increased, the drug loading of the antibiotic is also increased, ranging from 150 to 550 μg/cm 2 .
抗菌測試結果顯示,在含有生物高分子/抗生素複合鍍層試片上並沒有發現菌落數,也就是說在電化學沉積過程中並不會造成萬古黴素的變質而失去殺菌能力。The antibacterial test results showed that the number of colonies was not found on the test piece containing the biopolymer/antibiotic composite coating, that is to say, the vancomycin was not deteriorated and the sterilization ability was lost during the electrochemical deposition process.
抗生素釋放測試結果顯示,起初的爆發性釋放(initial burst)為55%,接著從第1天到第5天有20%穩定釋放(steady release),最後殘存25%是從6天至一個月後以更緩慢的速率釋放(slower release),表現在抗菌試驗中形成直徑30 mm~35mm的抑菌圈維持超過一個月。The antibiotic release test showed that the initial burst was 55%, followed by a 20% steady release from day 1 to day 5, and the last remaining 25% was from 6 days to a month later. At a slower release, the inhibition zone formed in the antibacterial test with a diameter of 30 mm to 35 mm was maintained for more than one month.
細胞培養測試顯示,將生物高分子/抗生素複合鍍層沉積在醫療用鈦合金植入材上可有效地加強骨母細胞的增殖、分化和礦化,此一結果顯示生物高分子的附加彌補了抗生素對骨細胞的負面影響。Cell culture tests have shown that the deposition of biopolymer/antibiotic composite coating on medical titanium alloy implants can effectively enhance the proliferation, differentiation and mineralization of osteoblasts. This result shows that biopolymers complement the antibiotics. Negative effects on bone cells.
幾丁聚醣是一種生物高分子,是地球上最豐富的天然多醣,因為它的生物相容性、生物降解性、親水性、無毒、抗菌性,使它已被廣泛應用於生物醫學工程。萬古黴素及健大黴素是一種廣效性抗生素,對革蘭氏陽性菌的活性有良好的治療和預防效果。基於幾丁聚醣和萬古黴素、健大黴素的優勢,醫界已將它們聯合使用於治療骨髓炎。本發明實驗雖以幾丁聚醣、明膠和萬古黴素、健大黴素為主,但具有此項技術之通常知識者,能依據本發明說明書所提供的揭露而衍生出不同形式的改變,包括生物高分子和抗生素的選用,或二種以上抗生素之混合。因此本發明實施例僅用以說明本案而已,非用以限制本案之範圍。舉凡不違本案精神所從事的種種修改或變化,俱屬本案申請專利範圍。Chitosan is a biopolymer and is the most abundant natural polysaccharide on earth. Because of its biocompatibility, biodegradability, hydrophilicity, non-toxicity and antibacterial properties, it has been widely used in biomedical engineering. Vancomycin and gentamicin are broad-spectrum antibiotics with good therapeutic and preventive effects against Gram-positive bacteria. Based on the advantages of chitosan and vancomycin, and gentamicin, they have been used in combination in the treatment of osteomyelitis. Although the experiment of the present invention is mainly based on chitosan, gelatin, vancomycin and gentamicin, those skilled in the art can derive different forms of changes according to the disclosure provided by the specification of the present invention. Includes the selection of biopolymers and antibiotics, or a mixture of two or more antibiotics. Therefore, the embodiments of the present invention are only used to illustrate the present invention and are not intended to limit the scope of the present invention. All kinds of modifications or changes that are not in violation of the spirit of the case are the scope of patent application in this case.
本發明所採用的工作電極均為有良好生物相容性與機械性質的醫療用金屬,這些醫療用金屬已廣泛運用於外科手術中,特別是在骨外科領域。本發明上述實驗結果顯示生物高分子之添加可提昇細胞貼附、增值、分化情形,它使骨科植入物表現出良好的骨整合能力;而生物高分子的添加亦顯著提高了抗生素載藥量,使醫療植入物能表現出更好的抗菌效果;除此之外,生物高分子的添加可提供抗生素較為緩慢的釋放效果,因此延長了抗生素的持續作用時間,並且期望在被植入者的體內維持均濃度的抗生素。The working electrodes used in the present invention are medical metals having good biocompatibility and mechanical properties, and these medical metals have been widely used in surgery, particularly in the field of orthopedics. The above experimental results of the present invention show that the addition of biopolymer can enhance cell attachment, proliferation and differentiation, and it enables orthopedic implants to exhibit good osseointegration ability; and the addition of biopolymer also significantly increases antibiotic drug loading. In addition, the medical implants can exhibit better antibacterial effects; in addition, the addition of biopolymers can provide a slower release of antibiotics, thus prolonging the duration of antibiotic action and expecting the implanted The body maintains an average concentration of antibiotics.
20...參考電極20. . . Reference electrode
30...輔助電極30. . . Auxiliary electrode
40...容器40. . . container
50...工作電極50. . . Working electrode
60...電解液60. . . Electrolyte
70...操作單元70. . . Operating unit
80...恆電位/電流儀80. . . Potentiostat/current meter
90...電腦90. . . computer
第一圖為本發明三極電化學系統配置示意圖。The first figure is a schematic diagram of the configuration of the three-pole electrochemical system of the present invention.
第二圖為本發明實施例一幾丁聚醣與健大黴素複合鍍層極化曲線圖。The second figure is a polarization curve of a composite coating of chitosan and gentamicin according to an embodiment of the present invention.
第三圖為本發明實施例二幾丁聚醣與萬古黴素複合鍍層極化曲線圖。The third figure is a polarization curve of the composite coating of chitosan and vancomycin according to the second embodiment of the present invention.
第四圖為本發明實施例三磷酸鈣鹽與明膠、健大黴素複合鍍層極化曲線圖。The fourth figure is a polarization curve of a composite coating of calcium triphosphate salt and gelatin and gentamicin according to an embodiment of the present invention.
第五圖為本發明的磷酸鈣鹽與膠原蛋白、萬古黴素複合鍍層極化曲線圖。The fifth figure is a polarization curve of the composite coating of the calcium phosphate salt, collagen and vancomycin of the present invention.
第六圖為本發明的幾丁聚醣與健大黴素複合鍍層掃描式電子顯微鏡觀察圖。The sixth figure is a scanning electron microscope observation view of the composite coating of chitosan and gentamicin of the present invention.
第七圖為本發明的幾丁聚醣與萬古黴素複合鍍層掃描式電子顯微鏡觀察圖。The seventh figure is a scanning electron microscope observation view of the composite coating of chitosan and vancomycin of the present invention.
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