201210651 六、發明說明： 【發明所屬之技術領域】 [0001] 本發明涉及一起搏器及其起搏器電極，尤其涉及—基於 奈米碳管之起搏器及其起搏器電極。 【先前技術】 [0002] 巴金森疾病（Parkinson’ s disease)係一慢性之中樞 神經系統失調疾病，病因目前仍不明，推測與腦細胞快 速退化，而無法製造足夠之神經傳導物質多巴胺 (Dopamine)有關。由於腦内需要多巴胺物質來達到指揮 肌肉活動’因此缺乏多巴胺會使病人產生活動障礙之症 狀，例如：震顫、僵直、運動遲缓等，進两影響了患者 之生活品質。 ........201210651 VI. Description of the Invention: [Technical Field] [0001] The present invention relates to a pacemaker and a pacemaker electrode thereof, and more particularly to a carbon nanotube-based pacemaker and a pacemaker electrode thereof. [Previous technique] [0002] Parkinson's disease is a chronic central nervous system disorder, and the cause is still unknown. It is speculated that brain cells rapidly degenerate and cannot produce enough neurotransmitter dopamine. related. Because dopamine is needed in the brain to command muscle activity, the lack of dopamine can cause symptoms of activity disorders, such as tremors, stiffness, and bradykinesia, which affect the quality of life of patients. ........
[0003] 目前’巴金森疾病除了藥物治療外，患者亦可利用外科 手術植入一腦部起搏器（brain pacemaker)來緩和病人 之不適症，通過腦部起搏器傳遞電子脈衝刺激腦部細胞 之方法’達到以控制之方式改變腦部活動之目的。 ◎ [麵]如圖1所示，先前腦部起搏器1包括一脈衝發生器1〇、一 起搏器電極11以及一連接線12。脈衝發生器1〇係用以產 生電脈衝訊號；起搏器電極11 一般由複數翻金屬電極線 構成，電極線表面包覆有絕緣層，電極線—端形成有一 不包覆絕緣層之鉑金屬刺激觸點，放置於腦部特定區域 ，用於傳遞電脈衝訊號以刺激腦細胞；連接線12為一包 覆有絕緣材料之電導線，用於連接起搏器電極丨丨與脈衝 發生器10 ;脈衝發生器10設置於患者身上，通過經頸部 繞到耳後之連接線12與起搏器電極11相連。脈衝發生器 099130431 表單編號A0101 第3頁/共24頁 0992053392-0 201210651 [0005] [0006] [0007] [0008] 099130431 1 0由一電池驅動而產生電脈衝訊號，訊號藉由連接線1 2 、起搏器電極11傳遞到腦部特定區域後釋放，從而干涉 神經細胞之活動以調節神經傳導物質之釋放，達到改變 腦部活動之目的。 由於先前技術中之起搏器電極11由鉑金屬電極線構成， 因此使起搏器電極（1)價格相對昂貴；（2)彈性不足 ，在活動中容易對人體組織造成損傷；（3)鉑金屬線做 之越細，其電阻率顯著增加，導致電脈衝訊號減弱，從 而對治療效果產生影響；（4)先前技術下，鉑金屬線無 法做得很細（如小於10微米），因此，可同時植入人體 内之電極線數量有限，從而能一次同時治療之區域有限 ，影響治療效果；（5)鉑金屬抗腐蝕性較弱，在人體長 期之活動中及體液之腐蝕下，易出現接觸不良等現象， 導致起搏器壽命縮短或治療效果降低。 【發明内容】 有鑒於此，提供一基於奈米碳管之起搏器及其起搏器電 極實為必要。 一種起搏器電極，包括至少一電極線，所述每一電極線 由一本體以及一絕緣層構成，絕緣層包覆於本體表面， 所述本體一末端具有一裸露部，其中，所述本體包括至 少一奈米碳管線，所述每一奈米碳管線包括通過凡得瓦 力首尾相連之複數奈米碳管。 一種起搏器，包括一脈衝發生器、一起搏器電極以及一 連接線，所述脈衝發生器、連接線、起搏器電極依次以 串聯之方式電連接，所述起搏器電極包括至少一電極線 表單編號A0101 第4頁/共24頁 0992053392-0 201210651 ’每—電極線由-本體以及_絕緣層構成，絕緣層包覆 於本體表面，所述本體—末端具有部，其中，所 述本體包括至少-奈米碳管線，所述每—奈米碳管線包 括通過凡得瓦力首尾相連之複數奈米碳管。 [_]與先前技術相比，本發日㈣述起搏器及其起搏器電極， 起搏器電極由至少一奈米碳管線構成，因此具有以下優 點·⑴使起搏器電極及起搏器整體成本降低；⑴ 起搏器電極具有更好之彈性，從而不易損傷人體組織； Ο (3)起搏器電極線具有更好之導·，尤其在起搏器電 極線較細之情況下’仍然具有良好&導電性；⑷奈米 碳管可以做得很細（如小於職米），因此起搏器電極 也可以做得很細，從而使得應用中可同時插人複數起搏 器電極以刺激不同之治療區域，達到更好之治療效果； (5)起射電極具有更好之韻録，賴延長起搏 之壽命並且保證治療效果。 【實施方式】 〇 [_]以下將結合附料細說明本發赌述起搏器及其起搏器 電極。 ⑽1]請參照圖2所示，本發明第一實施例提供一種起搏器2， 其包括一脈衝發生器2〇、一起搏器電極21以及—連接線 22。所述連接線22用於電連接所述脈衝發生器2〇及起搏 器電極21。所述脈衝發生器20發出之電脈衝訊號通過所 述連接線22與起搏器電極21作用於人體。 [0012]所述之脈衝發生器20包括外殼、電源、電脈衝發生電路 、控制電路、介面等。所述外殼材料為鈦金屬， 099130431 表單編號Α0101 第5頁/共24頁 ；保 °"2〇53392-〇 201210651 蔓/、内。p結構，所述電源用於為脈衝發生器提供動力， 衝令生電路用於產生電脈衝訊號，控制電路用於控 制所述電脈衝發生電路以產生不同之電脈衝訊號，所述 ”面用於與連接線22電連接。脈衝發生器產生之電脈衝 訊號藉由連接線22、起搏器電極21傳遞到腦部特定區域 後釋放，用於刺激標之細胞，例如腦部細胞C (如圖2所 示）或心臟肌肉細胞。 [0013] 请參照圖3及圖4，本實施例所述起搏器電極21包括至少 一電極線211，進一步，所述琴搏器電極21可包括一連接 端212及一固定件2 j 3。所述連接端2 j 2以及固定件η 3分 別套設於所述至少—電極線211相對之兩端、所述連接端 212為具有外螺紋之圓柱結構，其直徑根據起搏器電極？！ 直徑之不同為1毫米至3毫米，其材料為鉬金屬或鉑銥合 金。所述起搏器連接端可固定於人體内如腦殼、靠近心 臟之人體肌肉内等。所述電極線211可通過該連接端212 與連接線22電連接。所述固定件213固定於所述電極線 211之外表面，可嵌入到人體組織内，用於進—步固定所 述起搏器電極21，防止起搏器電極21從人體内滑動、脫 出。當所述起搏器電極21包括複數電極線211時，所述複 數電極線211平行緊密排列形成一束狀整體結構，連接端 212及固定件21 3分別套設於所述束狀整體結構相對之兩 端。 所述固定件213包括一固定環213a及複數固定翼213b， 其材料可為聚氣g旨（polyurethane)或高純石夕橡膠等且 有生物相容性之高分子材料。所述固定環2l3a為一圓筒 099130431 表單編號A0101 第6頁/共24頁 0992053392-0 [0014] 201210651 狀結構’所述固定翼213b為由該固定環213a之外表面向 遠離固定環213a之中心轴方向延伸之棒狀結構，其轴向 與固定環213a中心軸之夾角為30s至60s，且其延伸方向 為背離固定件213所在之電極線211之一端，從而形成倒 鉤結構。所述固定件213植入人體後，固定翼213b被人體 纖維組織包繞，從而進一步牢固之固定所述起搏器電極 21 〇 [0015] Ο ο [0016] 所述每一電極線211由一本體2111與一絕緣層2112構成 ’所述絕緣層2112包覆於本體2111之外表面。所述本體 2111—末端具有一裸露部2113，所述裸露部2113為所述 本體2111從絕緣層2112暴露出來之部分，裸露部2113之 長度可為0. 5毫米至2毫米。裸露部2113作為起搏器電極 21之刺激觸點，刺激觸點與人體細胞接觸，將脈衝發生 器20產生之電脈衝訊號傳遞到人體細胞。所述固定件2i3 設置於電極線211具有裸露部2113之一端。所述裸露部 2113與固定件213之間之距離可為3毫米至5毫米。所述 絕緣層2112為具有生物相容性之高分子材料，如聚氨酯 (polyurethane)、高純矽橡膠等。所述絕緣層2112 之厚度為1微米至50微米》 所述本體2111包括至少一奈米碳管線211 la，所述奈米 碳管線2111a之直徑範圍約為1微米至2〇〇微米，形成所 述本體2111直徑範圍為1微米至2毫米，優選之，所述本 體2111之直徑範圍為1微米至1〇微米。所述奈米碳管線 2111a可以為多根奈米碳管組成之非扭轉之奈米碳管線或 扭轉之奈米碳管線。 099130431 表單編號A0101 第7頁/共24頁 0992053392-0 201210651 [0017] 如圖5所示，該非扭轉之奈米碳管線包括複數沿奈米碳管 線轴向延伸並首尾相連之奈米碳管。優選之，該非扭轉 之奈米碳管線包括複數奈米碳管片段。該複數奈米碳管 片段通過凡得瓦力（Van de Waals Force)首尾相連 。每一奈米碳管片段包括複數相互平行並通過凡得瓦力 緊密結合之奈米碳管，且複數奈米碳管沿所述奈米碳管 線之軸向擇優取向延伸，所述奈米碳管可為單壁奈米碳 管、雙壁奈米碳管或多壁奈米碳管，或者係其組合。該 奈米碳管片段具有任意之長度、厚度、均勻性及形狀。 [0018] 如圖6所示，該扭轉之奈米碳管線包括複數繞奈米碳管線 軸向螺旋延伸之奈米碳管。優選之，該扭轉之奈米碳管 線包括複數奈米碳管片段。該複數奈米碳管片段通過凡 得瓦力首尾相連。每一奈米碳管片段包括複數相互平行 並通過凡得瓦力緊密結合之奈米碳管，且複數奈米碳管 沿所述奈米碳_管線之軸向螺旋狀旋轉延伸，所述奈米碳_ 管可為單壁奈米碳管、雙壁奈米碳管或多壁奈米碳管， 或者係其組合。該奈米碳管片段具有任意之長度、厚度 、均勻性及形狀。 [0019] 所述奈米碳管線可通過拉伸一奈米碳管陣列之方法製備 ，主要包括以下步驟： [0020] 首先，製備奈米碳管陣列，主要包括：（a)提供一平整 基底，該基底可選用P型或N型矽基底，或選用形成有氧 化層之矽基底，本實施例優選為採用4英寸之矽基底；（ b)在基底表面均句形成一催化劑層，該催化劑層材料可 選用鐵（Fe)、钻（Co)、錄（Ni)或其任意組合之合 099130431 表單編號A0101 第8頁/共24頁 0992053392-0 201210651 Ο [0021] 金之一；（c)將上述形成有催化劑層之基底在700~900 °(：之空氣中退火約30分鐘〜90分鐘；（d)將處理過之基 底置於反應爐中，在保護氣體環境下加熱到500 ~740°C， 然後通入碳源氣體反應約5〜30分鐘，生長得到奈米碳管 陣列，其高度大於1〇〇奈米，優選為1〇〇奈米〜10毫米。 在本實施例中，所述之奈米碳管陣列可以係單壁奈米碳 管陣列、雙壁奈米碳管陣列、多壁奈米碳管陣列或其混 合物，該奈米碳管陣列為複數彼此平行且垂直於基底生 長之奈米碳管形成之純奈米碳管陣列。可以理解，所述 奈米碳管陣列之製備方法還可以為電弧放電法、鐳射蒸 發法等其他方法。 Ο 其次，製備非扭轉或扭轉之奈米碳管線，其中，製備非 扭轉之奈米碳管線主要包括：（a )從奈米碳管陣列中選 取複數奈米碳管，在本實施例中，採用具有一特定寬度 之膠帶、一鑷子或一針尖接觸奈米碳管陣列以選定複數 奈米碳管；（b)以一特定速度沿垂直於奈米碳管陣列生 長方向拉伸所述複數奈米碳管，所述之複數奈米碳管在 拉力作用下沿拉伸方向逐漸脫離奈米碳管陣列之基底， 並且由於凡得瓦力作用，選定之複數奈米碳管分別與相 鄰之其他奈米碳管首尾相連地連續地被拉出，從而形成 奈米碳管線結構。 [0022] 而製備扭轉之奈米碳管線之方法為，將通過上述方法製 備之奈米碳管線結構黏附有拉伸工具之一端固定於一旋 轉電機上，扭轉該奈米碳管線結構，從而形成一扭轉之 奈米碳管線。進一步，可將通過上述方法製備之非扭轉 099130431 表單編號A0101 第9頁/共24頁 0992053392-0 201210651 或扭轉之奈米碳管線通過有機溶劑，或者通過高聚合物 溶液處理形成奈米碳管線聚合物，以進一步提高奈米碳 管線之強度。 [0023] [0024] [0025] 099130431 請參閱圖7及圖8，當所述本體2111包括複數奈米碳管線 2111a時’所述複數奈米碳管線2U la可緊密平行排列形 成一束狀結構或相互纏繞形成一束狀結構。圖7為本發明 所述本體2111由複數奈米碳管線2111a緊密平行排列形 成一束狀結構之示意圖。圖8為本發明所述本體2111由複 數奈米碳管線2111 a以零螺距之方式沿起搏器電極2丨之轴 向螺旋狀並行旋轉攤列形成柬狀結構之示意圖。 圖8所示之由複數奈米碳管線螺旋狀旋轉排列形成束狀結 構之本體2111可通過以下方法製備：將所述複數奈米碳 管線2111 a沿一支推轴（圖未示）軸向以零螺距之方式並 行旋轉排列，然後抽去支樓轴之方式形成；亦可通過將 複數奈米碳管線2111a —端固定，然後扭轉複數奈米碳管 線2111a另一端之方式形戍；耷可通過以相反方向之力同 時扭轉複數奈米碳管線21113¾兩端形成。由於起搏器電 極21中之奈米碳管線211 la為螺旋狀旋轉排列結構，因此 使起搏器電極21具有適當之強度，並使所述之起搏器電 極21在一定之強度下仍然具有較好之彈性。 請參照圖9，本實施例所述連接線22包括一線芯221、一 絕緣層222，所述絕緣層222包覆於所述線芯221之外表 面’其材料和厚度與前面所述絕緣層2112之材料相同。 進一步之，所述連接線22包括兩連接端223，所述兩連接 端2 2 3分別位於所述連接線2 2相對之兩端。所述線芯2 21 表單塢號A0101 第10頁/共24頁 <«92053392-0 201210651 可採用一金屬線，其材料為始金屬或始銥合金。咬者， 所述連接線22之線芯221可進一步採用與電極線21丨中本 體2111相同之結構和材料。所述兩連接端223為耳有内螺 紋之空心圓柱結構，其直徑、螺紋螺距與所述起搏器電 極21之連接端212相匹配，其材料為鉑金屬或鉑銥合金。 所述兩連接端223均與連接線22電連接，其中—連接端用 於與脈衝發生器20電連接，一連接端用於與起搏器電極 21之連接端212電連接。即所述脈衝發生器2〇、連接線 Ο [0026] 22以及起搏器電極21依次以串聯之方式電連接。 ..... . . ...... 實際生產中，所述連接線與起搏器電極也可以_體化製 備形成一體結構，所述一體結構之直徑可小於微米。 並且，一條連接線22可通過連接端2:23同時與複數起搏器 電極21電連接，所述複數起搏器電極21可將其連接端固 定於人體内如頭骨或靠近心臟之人體肌肉組織内。 [0027] ο 所述起搏器應用時’將起搏器電極之刺激觸點與待治療 區域之細胞C接觸’敏祕搏器脈衝發生器，連接線將脈 衝發生器產生之電脈衝訊號傳導顺電極，然後起 搏器電極將電脈衝訊號傳遞職療區域之細胞g，達到刺 激細胞之目之。根據病情需要，可同時使用複數起搏器 電極，每條_器電極分別接觸不同深度、不同位置之 治療區域。 [0028] 月所述起搏器及其起搏器電極，起搏器電極由至少 一奈米碳管線構成，因此，第_，可以使起搏器電極以 起搏器}體成本降低；第二，起搏器電極具有更好之 099130431 從而不易損傷人體組織；第三，使起 表早編號卿1 ^ π I/* 24 ! 0992053392-0 201210651 有更好之導電性，尤其在起搏器電極較細之情況下，仍 然具有良好之導電性；第四，奈米碳管可以做得很細（ 如小於Him，因此起搏器電極也可以做得很細，從 而使得應用中可同時插人複數起搏器電極以刺激不同之 治療區域，達収好之治療效果；第五，起搏器電極具 有更好之_储，能夠延長起㈣之壽命並且保證治 療效果。 [0029] [0030] +發明所述之起搏器可作為 ",e v urain pace — nmker)或心臟起搏器（cardiac pacemaker)。 综上所述’本發8㈣已符合發明專利之要件，遂依法提 出專利f請。惟’以上所述者僅為本發明之較佳實施例 f ’自不能減限财案之申請專概圍。舉凡熟悉本案 技藝之人士援依本發明之精神所叙等效修飾或變化， 皆應涵蓋於以下申請專利範圍内。 【圖式簡單説明】 [0031] [0032] [0033] [0034] [0035] [0036] [0037] 099130431 圖1係先前技術中起搏器之示意圖 圖2係本發明第一實施例所述起搏器之示意圖。 圖3係本發明第一實施例所 坩江起搏為電極之示意圖。 圖4係本發明第一實施例所 述起搏裔電極線之橫截面示意 圖〇 圖5係非扭轉之奈米碳管線之掃描電鏡照片。 圖6係扭轉之奈米碳管線之掃插電鏡照片。 圖7係複數奈米碳管線緊齊Λ 系在+订排列形成一束狀結構之示 表單編號Α0101 第12頁/共24頁 0992053392-0 201210651 意圖。 [0038] 圖8係複數奈米碳管線相互纏繞形成一束狀結構之示意圖 0 [0039] 圖9係本發明第一實施例所述起搏器連接線之示意圖。 [0040] 【主要元件符號說明】 起搏器：1，2 [0041] 脈衝發生器：10, 20 q [0042] 起搏器電極：11，21 [0043] 連接線：12,22 [0044] 電極線：211 [0045] 連接端：212，223 [0046] 固定件：213 [0047] 固定環：213a Q [0048] 固定翼：213b [0049] 本體：2111 [0050] 奈米碳管線：2111a [0051] 絕緣層：2112, 222 [0052] 裸露部：2113 [0053] 線芯：221 099130431 表單編號A0101 第13頁/共24頁 0992053392-0[0003] At present, in addition to medical treatment, patients with Parkinson's disease can also use a surgical brain implant a brain pacemaker to alleviate the patient's discomfort, and transmit electronic pulses through the brain pacemaker to stimulate the brain. The method of cells 'achieves the purpose of changing brain activity in a controlled manner. ◎ [Face] As shown in Fig. 1, the prior brain pacemaker 1 includes a pulse generator 1A, a pacemaker electrode 11, and a connecting wire 12. The pulse generator 1 is used to generate an electrical pulse signal; the pacemaker electrode 11 is generally composed of a plurality of metal electrode wires, the electrode wire surface is covered with an insulating layer, and the electrode wire end is formed with a platinum metal not covering the insulating layer. The stimulation contact is placed in a specific area of the brain for transmitting an electrical pulse signal to stimulate the brain cells; the connection line 12 is an electrical wire coated with an insulating material for connecting the pacemaker electrode and the pulse generator 10 The pulse generator 10 is disposed on the patient and is connected to the pacemaker electrode 11 by a connecting wire 12 that is wound around the ear through the neck. Pulse generator 099130431 Form No. A0101 Page 3 / Total 24 Page 0992053392-0 201210651 [0005] [0007] [0008] 099130431 1 0 is driven by a battery to generate an electrical pulse signal, the signal is connected by a line 1 2 The pacemaker electrode 11 is released after being delivered to a specific area of the brain, thereby interfering with the activity of the nerve cells to regulate the release of the nerve conduction substance, and to achieve the purpose of changing the brain activity. Since the pacemaker electrode 11 of the prior art is composed of a platinum metal electrode wire, the pacemaker electrode (1) is relatively expensive; (2) the elasticity is insufficient, and the human tissue is easily damaged during the activity; (3) platinum The finer the metal wire is, the more the resistivity is increased, which causes the electrical pulse signal to be weakened, which has an effect on the therapeutic effect; (4) In the prior art, the platinum metal wire cannot be made very fine (for example, less than 10 micrometers), therefore, The number of electrode lines that can be implanted into the human body at the same time is limited, so that the area of simultaneous treatment can be limited, which affects the therapeutic effect; (5) the corrosion resistance of platinum metal is weak, and it is easy to appear under the long-term activity of the human body and the corrosion of body fluids. Poor contact, etc., resulting in shortened pacemaker life or reduced therapeutic effects. SUMMARY OF THE INVENTION In view of the above, it is necessary to provide a carbon nanotube-based pacemaker and its pacemaker electrode. A pacemaker electrode comprising at least one electrode wire, the electrode wire is composed of a body and an insulating layer, the insulating layer is coated on the surface of the body, and the body has a bare portion at one end thereof, wherein the body The at least one nanocarbon pipeline is included, and each of the nanocarbon pipelines includes a plurality of carbon nanotubes connected end to end by a van der Waals force. A pacemaker includes a pulse generator, a pulsator electrode, and a connecting line, wherein the pulse generator, the connecting line, and the pacemaker electrode are sequentially electrically connected in series, and the pacemaker electrode includes at least one Electrode line form number A0101 Page 4 / Total 24 page 0992053392-0 201210651 'Every-electrode wire consists of a body and an insulating layer, the insulating layer is coated on the surface of the body, and the body has a portion at the end, wherein The body includes at least a nanocarbon line, and the per-nano carbon line includes a plurality of carbon nanotubes connected end to end by a van der Waals force. [_] Compared with the prior art, the present invention (4) describes the pacemaker and its pacemaker electrodes, and the pacemaker electrode is composed of at least one nano carbon line, thus having the following advantages: (1) making the pacemaker electrode and The overall cost of the beater is reduced; (1) the pacemaker electrode has better elasticity, so it is not easy to damage human tissue; Ο (3) The pacemaker electrode line has a better guide, especially when the pacemaker electrode line is thinner. The bottom 'still has good &conductivity; (4) the carbon nanotubes can be made very thin (such as less than the job), so the pacemaker electrodes can also be made very thin, so that the application can simultaneously insert multiple pacing The electrodes are used to stimulate different treatment areas to achieve better therapeutic effects; (5) The starting electrode has a better rhythm, which extends the life of the pacing and ensures the therapeutic effect. [Embodiment] 〇 [_] Hereinafter, the pacemaker and its pacemaker electrodes will be described in detail in conjunction with the materials. (10) 1] Referring to Fig. 2, a first embodiment of the present invention provides a pacemaker 2 comprising a pulse generator 2, a pulsator electrode 21, and a connecting line 22. The connecting wire 22 is for electrically connecting the pulse generator 2 and the pacer electrode 21. The electrical pulse signal from the pulse generator 20 acts on the human body through the connecting line 22 and the pacemaker electrode 21. [0012] The pulse generator 20 includes a housing, a power supply, an electrical pulse generating circuit, a control circuit, an interface, and the like. The outer casing material is titanium metal, 099130431 form number Α0101 page 5 / total 24 pages; guaranteed ° " 2〇53392-〇 201210651 vine /, inside. a p-structure, the power supply is used to power the pulse generator, the emergency circuit is used to generate an electrical pulse signal, and the control circuit is configured to control the electrical pulse generating circuit to generate different electrical pulse signals. The electrical pulse signal generated by the pulse generator is transmitted to the specific region of the brain through the connecting line 22 and the pacemaker electrode 21, and is used to stimulate the target cells, such as the brain cell C (eg, 2) or cardiac muscle cells. [0013] Referring to FIG. 3 and FIG. 4, the pacemaker electrode 21 of the embodiment includes at least one electrode line 211. Further, the pacer electrode 21 may include a a connecting end 212 and a fixing member 2 j 3. The connecting end 2 j 2 and the fixing member η 3 are respectively sleeved on opposite ends of the at least the electrode line 211, and the connecting end 212 is a cylinder having an external thread. The structure has a diameter of 1 mm to 3 mm depending on the diameter of the pacemaker electrode. The material is molybdenum metal or platinum-rhodium alloy. The pacemaker connection can be fixed in the human body such as the skull and the human body close to the heart. Intramuscular, etc. The wire 211 can be electrically connected to the connecting wire 22 through the connecting end 212. The fixing member 213 is fixed on the outer surface of the electrode wire 211 and can be embedded in the human tissue for step-fixing the pacemaker electrode. 21, preventing the pacemaker electrode 21 from sliding and coming out of the human body. When the pacemaker electrode 21 includes a plurality of electrode lines 211, the plurality of electrode lines 211 are closely arranged in parallel to form a bundle-like overall structure, and the connection end 212 And the fixing member 21 3 is respectively sleeved on opposite ends of the bundle-shaped integral structure. The fixing member 213 includes a fixing ring 213a and a plurality of fixing wings 213b, and the material thereof may be a polyurethane or a high-purity stone. a rubber material, etc., and a biocompatible polymer material. The fixing ring 231a is a cylinder 099130431 Form No. A0101 Page 6 / 24 pages 0992053392-0 [0014] 201210651 Shaped structure 'The fixed wing 213b is The outer surface of the fixing ring 213a extends in a direction away from the central axis of the fixing ring 213a, and the axial direction thereof is at an angle of 30 s to 60 s from the central axis of the fixing ring 213a, and the extending direction thereof is the electrode line 211 away from the fixing member 213. One end, thereby forming a barb structure. After the fixing member 213 is implanted into the human body, the fixing wing 213b is surrounded by the human fibrous tissue, thereby further firmly fixing the pacemaker electrode 21 [0015] ο ο [0016] Each of the electrode lines 211 is composed of a body 2111 and an insulating layer 2112. The insulating layer 2112 is coated on the outer surface of the body 2111. The body 2111 has a exposed portion 2113 at the end, and the exposed portion 2113 is 5毫米至2毫米。 The portion of the portion of the portion of the exposed portion of the layer 2, the exposed portion 2113 may be 0. 5 mm to 2 mm. The exposed portion 2113 serves as a stimulation contact of the pacemaker electrode 21, and the stimulation contact is in contact with human cells, and the electrical pulse signal generated by the pulse generator 20 is transmitted to the human body cells. The fixing member 2i3 is disposed on the electrode line 211 having one end of the exposed portion 2113. The distance between the exposed portion 2113 and the fixing member 213 may be 3 mm to 5 mm. The insulating layer 2112 is a biocompatible polymer material such as polyurethane, high purity ruthenium rubber or the like. The insulating layer 2112 has a thickness of 1 micrometer to 50 micrometers. The body 2111 includes at least one nano carbon line 211 la, and the nano carbon line 2111a has a diameter ranging from about 1 micrometer to 2 micrometers. The body 2111 has a diameter ranging from 1 micrometer to 2 millimeters. Preferably, the body 2111 has a diameter ranging from 1 micrometer to 1 micrometer. The nanocarbon line 2111a may be a non-twisted nano carbon line or a twisted nano carbon line composed of a plurality of carbon nanotubes. 099130431 Form No. A0101 Page 7 of 24 0992053392-0 201210651 [0017] As shown in FIG. 5, the non-twisted nanocarbon pipeline includes a plurality of carbon nanotubes extending axially along the carbon nanotube line and connected end to end. Preferably, the non-twisted nanocarbon pipeline comprises a plurality of carbon nanotube segments. The plurality of carbon nanotube segments are connected end to end by Van de Waals Force. Each of the carbon nanotube segments includes a plurality of carbon nanotubes that are parallel to each other and closely coupled by van der Waals, and the plurality of carbon nanotubes extend along an axially preferred orientation of the nanocarbon pipeline, the nanocarbon The tube can be a single-walled carbon nanotube, a double-walled carbon nanotube or a multi-walled carbon nanotube, or a combination thereof. The carbon nanotube segments have any length, thickness, uniformity and shape. [0018] As shown in FIG. 6, the twisted nanocarbon pipeline includes a plurality of carbon nanotubes extending axially around the nanocarbon pipeline. Preferably, the twisted carbon nanotube wire comprises a plurality of carbon nanotube segments. The plurality of carbon nanotube segments are connected end to end by a van der Waals force. Each of the carbon nanotube segments includes a plurality of carbon nanotubes that are parallel to each other and closely coupled by a van der Waals force, and the plurality of carbon nanotubes extend in a helical direction along the axial direction of the nanocarbon tube. The m-carbon tube can be a single-walled carbon nanotube, a double-walled carbon nanotube or a multi-walled carbon nanotube, or a combination thereof. The carbon nanotube segments have any length, thickness, uniformity, and shape. [0019] The nano carbon pipeline can be prepared by stretching a carbon nanotube array, and mainly includes the following steps: [0020] First, preparing a carbon nanotube array, mainly comprising: (a) providing a flat substrate The substrate may be a P-type or N-type germanium substrate, or a germanium substrate formed with an oxide layer. In this embodiment, a 4-inch germanium substrate is preferably used; (b) a catalyst layer is formed on the surface of the substrate, and the catalyst is formed. The layer material may be iron (Fe), drill (Co), recorded (Ni) or any combination thereof. 099130431 Form No. A0101 Page 8 / Total 24 Page 0992053392-0 201210651 Ο [0021] One of the gold; (c) The substrate on which the catalyst layer is formed is annealed in air at 700 to 900 ° (for about 30 minutes to 90 minutes; (d) the treated substrate is placed in a reaction furnace and heated to 500 to 740 in a protective gas atmosphere. °C, and then reacted with a carbon source gas for about 5 to 30 minutes to grow to obtain a carbon nanotube array having a height of more than 1 nm, preferably 1 to 10 mm. In this embodiment, The carbon nanotube array can be a single-walled carbon nanotube array, double a walled carbon nanotube array, a multi-walled carbon nanotube array or a mixture thereof, the carbon nanotube array being a plurality of pure carbon nanotube arrays formed parallel to each other and perpendicular to the substrate-grown carbon nanotubes. It is understood that The preparation method of the carbon nanotube array may also be an arc discharge method, a laser evaporation method, or the like. Ο Next, a non-twisted or twisted nano carbon pipeline is prepared, wherein the preparation of the non-twisted nano carbon pipeline mainly includes (a) selecting a plurality of carbon nanotubes from the array of carbon nanotubes, in this embodiment, using a tape having a specific width, a tweezers or a tip-contacting carbon nanotube array to select a plurality of carbon nanotubes (b) stretching the plurality of carbon nanotubes in a direction perpendicular to the growth direction of the carbon nanotube array at a specific speed, the plurality of carbon nanotubes gradually detaching from the carbon nanotubes in the stretching direction under tensile force The substrate of the array, and due to the effect of van der Waals force, the selected plurality of carbon nanotubes are continuously pulled out end to end with adjacent other carbon nanotubes to form a nanocarbon pipeline structure. [0022] system The twisted nano carbon pipeline is prepared by attaching one end of a nano carbon pipeline structure prepared by the above method to a rotating electric machine, and twisting the nano carbon pipeline structure to form a twisted nanometer. Carbon line. Further, non-twisting 099130431 Form No. A0101 Page 9 of 24 0992053392-0 201210651 or twisted nano carbon line prepared by the above method can be formed into an organic solvent or a high polymer solution to form a nanometer. Carbon line polymer to further increase the strength of the nano carbon line. [0025] [0025] Please refer to FIG. 7 and FIG. 8 when the body 2111 includes a plurality of carbon carbon lines 2111a. The nano carbon line 2U la can be closely arranged in parallel to form a bundle structure or intertwined to form a bundle structure. Fig. 7 is a schematic view showing the body 2111 of the present invention in which a plurality of nano carbon pipes 2111a are closely arranged in parallel to form a bundle structure. Fig. 8 is a schematic view showing the body 2111 of the present invention in which the plurality of carbon nanotubes 2111a are spirally rotated in parallel along the axis of the pacemaker electrode 2丨 in a zero pitch manner. The body 2111 of the bundle-shaped structure formed by spirally rotating the plurality of carbon carbon pipes shown in FIG. 8 can be prepared by the following method: the plurality of carbon nanotubes 2111 a are axially arranged along a thrust axis (not shown) It is formed by rotating in parallel in a zero pitch manner and then withdrawing the shaft of the branch; or by fixing the end of the plurality of carbon carbon lines 2111a, and then twisting the other end of the plurality of carbon carbon lines 2111a; Both ends of the plurality of carbon carbon lines 211133⁄4 are simultaneously twisted by the force in the opposite direction. Since the nanocarbon line 211 la in the pacemaker electrode 21 has a spiral rotation arrangement structure, the pacemaker electrode 21 has an appropriate strength, and the pacemaker electrode 21 still has a certain intensity. Better elasticity. Referring to FIG. 9 , the connecting wire 22 of the embodiment includes a core 221 and an insulating layer 222 . The insulating layer 222 covers the outer surface of the core 221 and has a material and a thickness and an insulating layer. The material of 2112 is the same. Further, the connecting line 22 includes two connecting ends 223, and the two connecting ends 2 2 3 are respectively located at opposite ends of the connecting line 22. The core 2 21 Form Dock A0101 Page 10 of 24 <«92053392-0 201210651 A metal wire can be used, which is made of a starting metal or a starting alloy. For the bite, the core 221 of the connecting wire 22 can further adopt the same structure and material as the body 2111 of the electrode wire 21丨. The two connecting ends 223 are hollow cylindrical structures with internal threads, and the diameter and the thread pitch are matched with the connecting ends 212 of the pacemaker electrodes 21, and the material thereof is platinum metal or platinum-rhodium alloy. The two connecting ends 223 are electrically connected to the connecting line 22, wherein the connecting end is used for electrically connecting with the pulse generator 20, and the connecting end is for electrically connecting with the connecting end 212 of the pacemaker electrode 21. That is, the pulse generator 2A, the connection line 0026 [0026] 22, and the pacemaker electrode 21 are sequentially electrically connected in series. ..... . . . In actual production, the connecting line and the pacemaker electrode may also be formed into a unitary structure, and the integral structure may have a diameter smaller than micrometers. Moreover, a connecting wire 22 can be electrically connected to the plurality of pacemaker electrodes 21 through the connecting end 2: 23, and the plurality of pacemaker electrodes 21 can fix the connecting end thereof to the human body such as a skull or human muscle tissue close to the heart. Inside. [0027] ο when the pacemaker is applied, 'contact the stimulation contact of the pacemaker electrode with the cell C of the area to be treated', and the connection line transmits the electrical pulse signal generated by the pulse generator. With the electrode, the pacemaker electrode transmits the electrical pulse signal to the cell g in the occupational therapy area to achieve the purpose of stimulating the cell. Depending on the condition, multiple pacemaker electrodes can be used at the same time, and each _ electrode is in contact with a treatment area of different depths and positions. [0028] The pacemaker and the pacemaker electrode thereof, the pacemaker electrode is composed of at least one nano carbon line, and therefore, the _, can reduce the body cost of the pacemaker electrode with a pacemaker; Second, the pacemaker electrode has a better 099130431 and thus is not easy to damage human tissue; third, make the table early number 1 1 π I / * 24 ! 0992053392-0 201210651 have better conductivity, especially in pacemakers In the case of thinner electrodes, it still has good electrical conductivity. Fourth, the carbon nanotubes can be made very thin (such as less than Him, so the pacemaker electrodes can also be made very thin, so that the application can be inserted simultaneously The person has multiple pacemaker electrodes to stimulate different treatment areas to achieve a good therapeutic effect; fifth, the pacemaker electrode has a better storage, can extend the life of (4) and ensure the therapeutic effect. [0029] [0030] The pacemaker described in the invention can be used as ", ev urain pace — nmker) or cardiac pacemaker. In summary, the '8 (4) of this issue has met the requirements of the invention patent, and the patent is filed according to law. However, the above description is only a preferred embodiment of the present invention. Equivalent modifications or variations of the person skilled in the art in light of the spirit of the invention are intended to be included within the scope of the following claims. BRIEF DESCRIPTION OF THE DRAWINGS [0037] FIG. 1 is a schematic diagram of a pacemaker in the prior art. FIG. 2 is a first embodiment of the present invention. [0037] [0037] FIG. Schematic diagram of a pacemaker. Fig. 3 is a schematic view showing the plucking of the Lijiang River as an electrode in the first embodiment of the present invention. Fig. 4 is a cross-sectional view showing the pulsating electrode line of the first embodiment of the present invention. Fig. 5 is a scanning electron micrograph of a non-twisted nanocarbon line. Figure 6 is a scanning electron micrograph of a twisted nanocarbon line. Figure 7 is a diagram showing the alignment of a plurality of nano carbon pipes in a + frame to form a bundle structure. Form No. 1010101 Page 12 of 24 0992053392-0 201210651 Intent. 8 is a schematic view showing a plurality of nano carbon lines intertwined to form a bundle structure. [0039] FIG. 9 is a schematic view showing a pacemaker connection line according to a first embodiment of the present invention. [Main component symbol description] Pacemaker: 1, 2 [0041] Pulse generator: 10, 20 q [0042] Pacemaker electrode: 11, 21 [0043] Connecting line: 12, 22 [0044] Electrode wire: 211 [0045] Connection end: 212, 223 [0046] Fixing member: 213 [0047] Fixing ring: 213a Q [0048] Fixed wing: 213b [0049] Body: 2111 [0050] Nano carbon line: 2111a [0051] Insulation: 2112, 222 [0052] Exposed: 2113 [0053] Core: 221 099130431 Form No. A0101 Page 13 / Total 24 Page 0992053392-0