200934543 九、發明說明： 【發明所屬之技術領域】 本發明相.-種絲力治療之照射裝置，尤指—種適用於 深層組織並且在錄大約為4〇5勤_具转核光效率之光動 力治療之照射裝置。 【先前技術】 ❹ 現今絲力治療的基本顧(見第1圖)是_病變組織内含 之光感物質(如座瘡内之座瘡桿菌)或將光感物質局部塗抹或靜脈 注射到病人身上，然後再以特定波長的光（通f是紅光）照射病 變組織，此時光能會經由光感物f轉移給組織内的其他物質，而 發生光化學_，進而產生對細财雜的分子喊賴瘤細胞 或其他病灶。由於光動力治療的基本構成要素是光感物質和激發 光源，因此必須要在這兩個要素的共同作用下才能產生療效。 ❹ -般而言’絲力雜_的激發統其波長是在可見 圍的非游雜輻射，所以光照本身並不會對身體產生任何毒 副作用，光動力治療所使用的光感藥物必須經過特定波長的 光激發後，才會在照射的部位產生細胞毒性，換句話說，光動 治療所使㈣光«物和激發光在分職形時，完全沒有 也沒有任何毒性。只有當二者碰在—起時，才會有療效。除此之 外，近年來的研究更顯示出，光動力治療尚能摧毀_的血 阻絕其血賴應’更能活化人_免_統，增加_免疫力以 200934543 對抗癌細胞。另一方面除了癌腫瘤治療之外，現有之光動力治療 也陸續的被應用於疲、痤瘡、美容及獸醫等用途。 然而’目前的光動力治療也不是沒有缺點，由於光在組織 ' 内的透射率普遍不佳(如第2A圖所示），其能量在組織内依距 離深度呈指數型式遞減，因此對於較深的病灶，其治療的效果 並不好。雖然多數光感物質對波長較短的紫光較敏感(例如第 ❹ 2A圖中Photofrin的Soret band)，為了達到較深層的治療效果，200934543 IX. Description of the invention: [Technical field to which the invention pertains] The invention relates to an illumination device for the treatment of silk force, in particular, for a deep tissue and recorded at about 4 〇 5 _ 具 核 核 核 _ Illumination device for photodynamic therapy. [Prior Art] 基本 The basic consideration of silk therapy today (see Figure 1) is the light-sensitive substance contained in the diseased tissue (such as the acne bacillus in the acne) or the topical application or intravenous injection of the light-sensitive substance to the patient. The body then irradiates the diseased tissue with light of a specific wavelength (passing f is red light), at which time the light energy is transferred to other substances in the tissue via the light-sensing substance f, and photochemical _ occurs, thereby producing a fine-grained The molecule calls for tumor cells or other lesions. Since the basic components of photodynamic therapy are light-sensitive substances and excitation light sources, it is necessary to combine the two elements to produce therapeutic effects. ❹ - Generally speaking, the excitation of 'silk force' is the non-half radiation in the visible range, so the light itself does not cause any toxic side effects to the body. The photo-sensitive drugs used in photodynamic therapy must be specific. After the excitation of the wavelength of light, cytotoxicity will occur at the irradiated part. In other words, the phototherapy will make the (four) light and the excitation light have no toxicity at all. Only when the two encounter it will have a curative effect. In addition, recent studies have shown that photodynamic therapy can still destroy _ blood stasis and blood reliance should be more able to activate human _ _ _ system, increase _ immunity to 200934543 against cancer cells. On the other hand, in addition to cancer tumor treatment, existing photodynamic therapy has been applied to fatigue, acne, beauty and veterinary applications. However, 'the current photodynamic therapy is not without its drawbacks. Because the transmittance of light in the tissue is generally poor (as shown in Figure 2A), its energy decreases exponentially in the tissue according to the depth of the distance, so it is deeper. The lesions are not well treated. Although most light-sensitive substances are sensitive to violet light with a shorter wavelength (for example, the Soret band of Photofrin in Figure 2A), in order to achieve a deeper therapeutic effect,
在目前的光動力治療多採用組織透射率較高的紅光(見第2A 圖）’目前最深的治療深度大約可以達到一公分深。亦有採用較 -短波長的藍光設計，但因其波長對組織的透射率較低，即使採 用較高能量之藍光雷射二極體做為光源也僅適用於痤瘡(不外 加光感物質)等的淺層治療用途，加以藍光雷射因具有單價太 高、壽命有限、功率太低並且不易取得等缺點，而不符合經濟 效益。 為改善前述光源在組織内的有限穿透深度’在習知技藝中往 往透過聚焦-矩陣光源以提高單位面積内光照的能量(第3圖），或 以矩陣光源直接照射以提高照光均勻性(第4A圖）。但皮膚、肌肉、 臟器等組織(以下簡稱組織)之折射率多半在！ 4附近(第4b圖），明 顯大於空氣(折射率=1)，光在組織表面會發生反射、散射等現象而 導致入射效率大幅降低。另—方面組織表面魏往往非平面，造 成光入射肢產生柯麵變絲辟场率碰絲差的入射 200934543 均勻性。其中，光從不同角度照射皮膚的透射率變化可由第5圖 可看出。 . ‘ 因此’需要-套照明裝置搭配適當的光感物質，使其能夠有 *效的將具有最佳錄的激發光以能量㈣且足触度的照射而深 入組織内，以達到最理想的光動力治療功效。 ^ 【發明内容】 因此’本發明之一目的在於提供一種在380nm〜430nm波長範 圍具有最大發光效率(見帛9目)之魏銘鎵銦(AiInGaN)發光二極 體(LED)作為照射光源’並配合在相同波長範圍有最佳吸收帶的原 紫質等紫質族系光感物質之光動力治療之照射裝置。 本發明之又一目的在於提供一種光動力治療之照射裝置，該 照射裝置透過最前端光學組件(以下簡稱光傳導物件)之出光面直 ®接接觸域’可有崎低隨織騎率絲面龍造成的光反射 損失及光入射不均勻問題，並同時降低了該光傳導物件出光面之 内部反射。 本發明之又一目的在於提供一種光動力治療之照射裴置，該 照射裝置之光傳導物件表面為柔軟可透光賴，明貼附於各種 型貌之組織表面’更可以液體或膠體填充於光傳導物件與組織接 觸面之間隙’以進-步降低因組織表面細微變化(如皮膚表面纹路) 200934543 造成之氣泡等微間隙引起的光散射。 本發明之又一目的在於提供一種光動力治療之照射裝置，透 過光傳導物件對喊施加壓力以排除喊局部之血液，可有效降 低因組織内血液中血紅素吸收照射光源而造成入射光能量的損 失。 、 ❹ 本發明之又—目的在於提供-種光動力治療之騎裝置，透 過接觸組織之光料物件可賴射雜提供冷、熱㈣音波振動 以降低治療之不適或提高光動力治療之效果。 本發明之又—目的在於提供-種光動力治療之照射裝置，a 接觸組織之光傳導物件或該光解物件之表面為可替換結構，以、 達到替換或分離消毒之目的。 ^發明之X-目的在於提供—種光動力治狀騎裝置，可 利用谷ϋ内之液體料料介質，可將組織浸泡於魏體令以達 到均勻入射之目的。 本發明之又· 目的在於提供一種光動力治療之照射裝置，利 用一光源·m以掌握及控繼射光源之亮度 ，並可瞭解光源老 化狀況而適時更替。 【實施方式】 200934543 明參考第6圖為本發明光動力治療（ph〇t〇(jynamic Therapy， PDT)之照射裝置之第一較佳實施例，本實施例之照射裝置用於 照射一被施予紫質族系光敏感劑或其前驅體6〇5之組織6〇6。本實 施例之照射裝置可包含一發光二極體(LED)光源6(n、一電源及調 控迴路602、-反射鏡603及一光學鏡面6〇4，其巾，該發光二極 體601發出的光線經由反射鏡6〇3及光學鏡片6〇4將光線投射於 已投藥(例如可為紫質族系光敏感劑或其前驅體6〇5)之組織6〇6。 ⑮其中’该發光二極體601可為氮化紹鎵銦(AiInGaN)發光二極體。 其中’紫質族系(porphyrin，又名卟啉)光敏感劑或其前驅體6〇5指 任一種含外吩(porphin)結構的化合物，在紫光或近紫外光波段有強 烈的吸收峰一般稱之為S〇retBand為其光學特徵(見第7A圖）。此 強烈吸收峰多數落在波長38〇nm〜430nm之間，第7B圖中顯示部 份紫質族系光敏感劑或其前驅體605之最佳吸收波長。多種紫質 族系光敏感劑或其前驅體6〇5在吸收光的能量之後，其能量可轉 φ 移至氧分子而造成有極強生物毒性的單相氧自由基，適合於作為 光動力治療及光動力診斷的光感物質，在第2B圖中之光敏感劑多 屬紫質族系光敏感劑或其前驅體605並且其soret Band也落在相 同波長範圍。 兔處族糸光敏感劑中以原紫質（Protoporphyrin，ΡρΙΧ，又名 原°卜琳）為最具代表性之光感物質，其具有吸收學約在4〇5nm_ 近、無明顯組織排斥現象、對病變組織有高選棒比等特性，有利 於選擇性治療’其中氨基酮戊酸（Aminolevulinic Acid,簡稱ALA、 200934543 5-ALA、^ALA)為原紫質理想之前趨體（preeursQr)，因其分子 量較低而易於在組織中渗透及擴散，利於投藥，其 目 圖。半導體類發光原件具有波長分佈集中、功率可調整:體積小、 發熱有限、單價低以及容易大量生產等優點，非常適合作為光動 力治療之絲。其他適合於紫_系錄_或其前驅體之Met Band之較短波長之其他半導體類發光原件還可包含有冚族氮化 物（氮化鋁鎵銦）發光二極體、IMV族化合物（氧化鋅、硫化鋅、 φ硒化鋅等）發光二極體及電致發光(EL)等。 本實施例之發光一極體採用氮化紹嫁銦族系發光二極體 601 ’且該族系發光二極體波長峰值介於38〇奈米（nm)至幻^ 奈米之間。雖然該族系發光二極體一般應用於藍、白及綠光， 但其最佳之光電轉換效率(外部量子效益)恰發生在波長大約為4〇5 nm附近的紫光或近紫外光區域(見第9圖），剛好落在多數紫質族 ◎系光敏感劑或其前驅體605的Soret Band分饰範圍。由於半導體 類發光一極體的光譜集中，可讓大部分的能量落在紫質族系的最 佳吸收帶中(見第10圖），尤其最近數年間，在4〇5nm附近的氮化 鋁鎵銦族系發光二極體601的發光功率已達到大於100mW，明顯 優於同波長之雷射二極體，並且氮化銘鎵銦族系發光二極體 在價格及產品壽命上均優於雷射二極體。因此，以氮化鋁鎵銦族 系發光二極體601作為激發光源配合紫質族系光敏感劑或其前驅 體605，實為各種最佳化條件之交集。此外，本實施例之照射裝置 更可裝設一具有630奈米波長或其他可見光之發光二極體光源， 11 200934543 用以作為獅光源，加強對組織深處之照射功效。 胃參考第11圖為本發明光動力治療（ph〇t〇dynamicTherapy, PDT)之照射裝置之第二概實施例。本實施例之照射裝置用於 …、射被施予紫質族系光敏感劑或其前驅體1107之組織。本實施 例之照射裝置可包含—發光二極體光源疆…電源及調控迴路 1102實〜壓克力（聚曱基丙烯酸甲醋、PMMA)光引導物件 ❹1103、-光傳導物件11〇4。其中’實心壓克力光引導物件聰之 表面具有一全反射面，光傳導物件1HH之表面具有-出光面，並 且光傳導物件1104材質可為玻璃、塑膠、pc、壓克力（聚甲基丙 烯酸甲S曰、PMMA)、石夕膠、液體填充物、膠體填充物或柔軟石夕膠。 .在本實施财，光傳導物件1UM之材·㈣軟謂加以說明。 一般而言，只要光經過兩折射率不同介質之介面，即會因反 ❹射、散射等翻造成光能量損失(以下簡稱折射率損失）。介面兩端 之折射率差騎大此獅率損失愈高，尤其從高折神端至低折 射率端甚至胃發生全反射現象崎成最大之折㈣損心本實施 例帽使用之實心屢克力光引導物件11〇3及柔軟石夕膠光傳導物件 1104之折射率約略相同(〜15) ’光自發光二極體光源_射出後 不會經過任何空氣㈣)_，因此，實心PMMA光引導物件聰 及柔軟雜導物件測可視為單—光學結繼，幾無光路徑 折射率損失。但當光傳導至柔軟石夕膠光傳導物件1104之表面時， 光自高折射率端進入折射率為！之空氣時造成第一折射率損失(見 12 200934543 笫12圖），而自空氣再近入組織(n〜14，如第4B圖)時又發生第二 折射率損失(見第5圖），而折射率總損失係為第一折射率損失加 • 上第二折射率損失之總和。若將此柔軟矽膠光傳導物件11〇4之出 光面直接接觸於組織，使該柔軟矽膠光傳導物件11〇4與組織ιι〇6 無空氣間蜍，則僅有一次折射率損失(見第13圖），並且該一次折 射率損失明顯低於光自柔軟矽膠光傳導物件11〇4進入空氣再由空 氣進入組織1106之損失。 〇 但部份組織如皮膚表面有細微之紋路，在柔軟矽膠光傳導物 件1104與組織1106間，勢必有細微之空氣間隙發生。為減少此 類型之折射率損失，可在組織1106之表面塗佈一光媒介物質 11〇5(例如，水、透明之液體或更易操作之膠狀或膏狀物質），如此 可徹底消除柔軟珍膠光傳導物件的出光面與組織之間的細微空氣 間隙，進一步降低折射率損失。依光學原理，此光媒介物質ιι〇5 〇之折射率’最好介於柔軟矽膠光傳導物件1104與組織1106之間， 其數值約為1.33〜1.55 (見第14圖）。在此光媒介物質11〇5存在的 條件下可大幅降低大角度的折射率損失，如第15圖所示，因此可 改善因組織表面形貌及光源入射角度變化造成的入射不均勻現 象。 0月參考第16圖為本發明光動力治療（Ph〇t〇dynamic Therapy， PDT)之照射裝置之第三較佳實施例。本實施例之照射裝置用於 照射一被施予紫質族系光敏感劑或其前驅體1607之組織。本實施 13 200934543 例之照射裝置可包含一發光二極體光源16〇1、一電源及調控迴路 1602、一實心壓克力光引導物件1603、一反射鏡面16〇4及一液體 填充囊體1605。在本實施例中以柔軟液體填充囊體作為光傳導物 件，其柔軟並具彈性之表面可輕易貼附於多數形貌之組織16〇6。 並且可利用管路165卜1652，將冷、熱液體輸人該液體填充囊體 中，如此可對治療部位之組織1606進行冷、熱敷以減輕治療造成 的疼痛或不適。 請參考第17圖為本發明光動力治療（ph〇t〇dynamicTherapy， PDT)之照射裝置之第四較佳實施例。本實施例之照射裝置用於 照射一被施予紫質族系光敏感劑或其前驅體之組織。本實施例之 照射裝置包含一發光二極體(LED)光源1701、一電源及調控迴路 1702、一實心壓克力光引導物件17〇3、一反射鏡面17〇4及一振動 裝置1705。因為發現，人體組織中對於光的吸收主要來自於血液 中的血紅素，第18圖為人體組織(乳房)的各波長吸收光譜，和其 他多數組織一樣可以明顯的可以看出其在略大於4〇〇nm及55〇nm 附近的兩個強烈吸收峰完全吻合於第19圖中血紅素及帶氧血紅素 的吸收特徵’而其略大於400nm的強烈吸收峰即為血紅素的soret Band。在本實施例中’用實心壓克力光引導物件17〇3施與適當程 度的壓力於該接觸部位可輕易排除組織1708内局部之血液，以降 低血紅素對入射光的吸收’尤其是在400nm附近的波長。而當壓 力釋放時周邊的血液將回流以補充光動力治療所需的氧。而重覆 此壓迫照光以及釋放壓力之過程，如同水泵般不斷的交換富氧之 14 200934543 血液進入照射區域，可持續補充因為光動力治療消耗掉的氧。 如第π圖所示’本實施例之振動裝置可為壓電原件或偏心輪 等任何可產生娜讀域置聰。朗光解婦m6將振動 傳遞至組織 ’可降低治療時之不適，並且因振動而提高分子 碰撞機率，亦可增進光動力治療之效果。另外，本實施例之光傳 導物件具有固體微粒1707，以作為光擴散結構，該固體微粒17〇7 〇成份可為氧化鋁(A1203)、氧化鋅(Zn〇)、銳鈦礦相(3她祀細e) 之二氧化鈦(Τι02)等折料不同於光料物件讀料，可造成光之 散射，以達到極佳之照射均勻性。 請參考第20圖為本發明光動力治療（ph〇t〇dy_ic勤_， PDT)之照射裝置之第五較佳實關。本實關之照射裝置用於 照射一被施予紫質族系光敏感劑或其前驅體之組織。本實施例之 照射裝置包含-發光二極體光源細、一電源及調控迴路2〇〇2、 一反射鏡面2003、一光傳導液體容器2〇〇4、一固體微粒2〇〇5及 一光偵測器2006。其中，光傳導液體容器2〇〇4裝有一光傳導液體 2007 ’並且光傳導液體2〇〇7内掺雜固體微粒2〇〇5。因光傳導液體 2007折射率大於空氣，光線易被反射回光傳導液體2〇〇7 ,再加上 固體微粒2005的散射作用，此光傳導液體2〇〇7内充滿各方向均 勻的光線。組織2008浸泡於此液體中，各位置及角度都可獲得均 勻I1生甚佳的照射，特別適用於形狀極不平坦的組織。其中， 光線偵測器2006耦合於光傳導液體容器2〇〇4用以偵測該光傳導 15 200934543 液體2007内光輸出狀況，產生偵測訊號來調整電流，亦可透過迴 路進行自動光強度控制’甚或程序化的光強度控制，如此可充分 掌握光照射計量。光線侧器2006若有波長偵測功能則更可用以 掌握光源老化狀態，適時更換光源。 無論以上任何-種設計，其光傳導物件时料為易與發光 二極體等電子元件分_可拆麟換結構(例如，光料物件^一 ©可分離之彼覆物件），如此僅將接觸組織之部份分開消毒或抛棄， 可避免在赫作業時損害f子元件。當然亦可能採用翻可替換 之薄片或薄膜覆蓋於光傳遞物件表面達到相同功效。 、 以上諸實關僅為轉明相咖念及方法之财，各概念及 方法均可交又配合使用，並不囿於所揭露之諸實施例。 〇 以上所述僅為本發明之較佳實施例，凡依本發明申請專咐 圍所做之均等變化與修飾，皆應屬本發明之涵蓋範圍。 【圖式簡單說明】 第1圖為典型光敏感劑在光線激發下之光動力反應程序。 第2A圖為人體组織的透射率(虛線)及ph〇t〇frin光感物質 (圖左多峰實線)與先波長之關係。 第扭圖為目前已商業化之光動力治療用光感物質與其習用之 發波長。 16 200934543 第3圖為先前技術之照射裝置。 第4A圖為先前技術之照射裝置。 第4B圖為皮膚、肌肉、臟器等組織之折射率。 ^圖為光自空氣人射皮膚之光透射率與其人射角⑼的關係。 第6圖為本發明之第—難實糊之示細。 第从圖為紫質典型之吸收光譜，在4〇〇nm附近之最強吸收峰為 其 Soret Band。 〇第7B圖為部份紫質(口卜琳)的最強吸收峰(SoretBand)波長。 第8圖為ALA-PpIX在組織内的代謝流程。 第圖表不市售氮化紹鎵銦族系咖的光電轉換效率(外部量子效 率)與波長分佈關係’可明顯看出在4〇5細附近之發光效 率最佳，而此範圍與多數紫質380肺〜430nm的SoretBand 分佈範圍重疊。 =10圖為典型的405nm氮化叙鎵銦LED的光譜及ρρΐχ吸收光譜。 φ 11圖為本發明之第二較佳實施例之示意圖。 =圖表示光自㈣,5透騎料_射出_與人㈣度之關係。 圖表示光自η=1.5透明材料内部射出至W.4組織之透射比 例與入射角度之關係。 第14圖旦為模型計算光媒介物質的折射率⑻對光能量總入射率的 ”曰其巾LED曰曰粒(chip)的光場採用lambertian光場模 1光傳導物件及組織折射率分別假設為1.5及1.4。 圖為模型汁算光媒介物質的折射率為W及無光媒介物質 (n U各肖度人射光能量的差異，其巾光源(LED_ehip)的光 17 200934543 場採用lambertian光場模型，光傳導物件及組織折射率分 別假設為1.5及1.4。 第16圖為本發明之第三較佳實施例之示意圖。 第17圖為本發明之第四較佳實施例之裝置圖。 第18圖為人體乳房的各波長吸收係數。 第19圖為人體血紅素之吸收係數與波長關係。 第20圖為本發明之第五較佳實施例之示意圖。 ❿ 【主要元件符號說明】 氮化銘鎵銦(AlInGaN)發光二極體601 電源及調控迴路 602、1102、1602、1702、2002 反射鏡 603、1604、1704、2003 光學鏡面604 紫質族系光敏感劑或其前驅體605、1107、1607 ^ 組織 606、1106、1606、1708、2008 發光二極體 1101、16(H、1701、2001 實心壓克力光引導物件1103、1603、1703 光傳導物件1104、1706 光媒介物質1105 液體填充囊體1605 管路 1651、1652 固體微粒1707、2005 振動裝置1705 18 200934543 排除血液方向1709 光傳導液體容器2004 光偵測器2006 光傳導液體2007In current photodynamic therapy, red light with a high tissue transmittance is used (see Figure 2A). The deepest treatment depth is currently about one centimeter deep. There is also a blue light design with a relatively short wavelength, but because of its low wavelength to tissue transmittance, even a higher energy blue laser diode is used as a light source only for acne (no light sensitive substance) For shallow therapeutic applications, the use of blue-light lasers has disadvantages such as high unit price, limited life, low power, and difficulty in obtaining, and is not economical. In order to improve the limited penetration depth of the aforementioned light source in the tissue, in the prior art, the focus-matrix light source is often used to increase the energy of illumination per unit area (Fig. 3), or directly illuminated by a matrix light source to improve illumination uniformity ( Figure 4A). However, the refractive indices of tissues such as skin, muscles, and organs (hereinafter referred to as tissues) are mostly in the world! Near 4 (Fig. 4b), it is clearly larger than air (refractive index = 1), and light is reflected and scattered on the surface of the tissue, resulting in a significant decrease in incident efficiency. On the other hand, the surface of the tissue is often non-planar, resulting in the incidence of light incident on the surface of the surface of the surface. 200934543 Uniformity. Among them, the change in transmittance of light from different angles of the skin can be seen in Figure 5. 'Therefore' need to - set the lighting device with the appropriate light-sensitive substance, so that it can be optimally illuminated with the best recorded excitation light in energy (four) and foot touch to penetrate into the tissue to achieve the best Photodynamic therapy efficacy. SUMMARY OF THE INVENTION Accordingly, it is an object of the present invention to provide an AiInGaN light-emitting diode (LED) having a maximum luminous efficiency (see 目9 mesh) in the wavelength range of 380 nm to 430 nm as an illumination source' An illumination device for photodynamic therapy of a purple-based light-sensitive substance such as protoplast having an optimal absorption band in the same wavelength range. Another object of the present invention is to provide an illumination device for photodynamic therapy, which can pass through the front end optical component (hereinafter referred to as a light-conducting object), and the light-emitting surface can be connected to the contact area. The light reflection loss caused by the dragon and the uneven incidence of light, and at the same time reduce the internal reflection of the light-emitting surface of the light-conducting object. Another object of the present invention is to provide an illumination device for photodynamic therapy, wherein the surface of the light-conducting object of the illumination device is soft and permeable, and the surface of the tissue attached to various shapes can be filled with liquid or colloid. The gap between the light-conducting object and the tissue contact surface is used to further reduce the light scattering caused by micro-gap such as bubbles caused by fine changes in the surface of the tissue (such as skin surface texture). Another object of the present invention is to provide a photodynamic therapy illumination device that applies pressure to a shunt through a light-conducting object to eliminate local blood, thereby effectively reducing the incident light energy caused by the absorption of the illumination source by the hemoglobin in the blood of the tissue. loss. ❹ ❹ ❹ 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 目的 光 光 。 光 光 光 光 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 Still another object of the present invention is to provide an illumination device for photodynamic therapy, wherein the surface of the light-conducting article contacting the tissue or the surface of the photoly-decomposed article is a replaceable structure for the purpose of replacement or separation sterilization. ^Inventive X- The purpose is to provide a kind of photodynamic treatment device, which can use the liquid material medium in the gluten to soak the tissue in the body to achieve uniform incidence. Still another object of the present invention is to provide an illumination device for photodynamic therapy using a light source m to grasp and control the brightness of the secondary light source, and to understand the aging condition of the light source and to replace it at the right time. [Embodiment] 200934543 A reference to Fig. 6 is a first preferred embodiment of a photodynamic therapy (PDT) illumination device according to the present invention. The illumination device of the embodiment is used for illumination. The light-emitting device of the purple-based light-sensitive agent or its precursor 6〇5 is 6〇6. The illumination device of the embodiment may include a light-emitting diode (LED) light source 6 (n, a power supply and control circuit 602, - The mirror 603 and an optical mirror 6〇4, the towel, the light emitted by the LED 601 projects the light through the mirror 6〇3 and the optical lens 6〇4 (for example, it can be purple light The sensitizer or its precursor 6〇5) has a structure of 6〇6. 15 wherein the light-emitting diode 601 can be a gallium nitride (AiInGaN) light-emitting diode. Among them, the porphyrin family (porphyrin) The porphyrin light-sensitive agent or its precursor 6〇5 refers to any compound containing a porphin structure, and has a strong absorption peak in the violet or near-ultraviolet light band, which is generally called S〇retBand as its optical characteristic. (See Figure 7A.) This strong absorption peak mostly falls between the wavelengths of 38〇nm~430nm, as shown in Figure 7B. The optimal absorption wavelength of some purple-type photo-sensitive agents or their precursors 605. After the absorption of light energy, a variety of purple-type photo-sensitive agents or their precursors can be transferred to oxygen. Molecular and single-phase oxygen radicals with strong biotoxicity, suitable as photo-sensing substances for photodynamic therapy and photodynamic diagnosis. The photo-sensitive agents in Figure 2B are mostly purple-type photo-sensitive agents or Precursor 605 and its soret band also fall in the same wavelength range. Among the rabbit glare sensitizers, Protoporphyrin (Proptophyrin, also known as the original 卜Blin) is the most representative light-sensitive substance, which has Absorption is about 4〇5nm_ near, no obvious tissue rejection, high selectivity to the diseased tissue, etc., which is beneficial to the selective treatment of 'Aminolevulinic Acid (ALA, 200934543 5-ALA, ^) ALA) is a pre-puriner precursor (preeursQr), which is easy to permeate and diffuse in tissues due to its low molecular weight, which facilitates the administration of drugs. The semiconductor-based luminescent element has a concentrated wavelength distribution and adjustable power: small volume. , It has the advantages of limited heat generation, low unit price and easy mass production, and is very suitable as a filament for photodynamic therapy. Other semiconductor-based illuminating elements suitable for the shorter wavelength of the Met Band of the purple _ _ _ or its precursor may also include冚-nitride (aluminum gallium nitride-indium) light-emitting diode, IMV group compound (zinc oxide, zinc sulfide, φ-selenide, etc.) light-emitting diode, electroluminescence (EL), etc. The one-pole body adopts a nitrided indium-based light-emitting diode 601' and the wavelength peak of the family of light-emitting diodes is between 38 nanometers (nm) and magical nanometer. Although this family of light-emitting diodes is generally applied to blue, white and green light, its optimal photoelectric conversion efficiency (external quantum benefit) occurs in the violet or near-ultraviolet region near the wavelength of about 4〇5 nm ( See Figure 9), which falls within the Soret Band sub-decoration range of most purple quinone photo-sensitive agents or their precursors 605. Due to the spectral concentration of the semiconductor-based light-emitting body, most of the energy falls in the optimal absorption band of the purple family (see Figure 10), especially in recent years, aluminum nitride near 4〇5nm. The luminous power of gallium indium-based light-emitting diode 601 has reached more than 100mW, which is obviously superior to the laser diode of the same wavelength, and the nitrided indium-indium-based light-emitting diode is superior in price and product life. Laser diode. Therefore, the use of the aluminum gallium indium-inductive family of light-emitting diodes 601 as an excitation light source in combination with a purple-type photo-sensitive agent or its precursor 605 is an intersection of various optimization conditions. In addition, the illumination device of the embodiment can be further equipped with a light-emitting diode light source having a wavelength of 630 nm or other visible light, and 11 200934543 is used as a lion light source to enhance the illumination effect on the deep tissue. Stomach Reference Fig. 11 is a second embodiment of an apparatus for illuminating a photodynamic therapy (PDT) of the present invention. The irradiation apparatus of this embodiment is used for ... the tissue to which the purple-type photo-sensitive agent or its precursor 1107 is applied. The illumination device of this embodiment may comprise a light-emitting diode source... a power supply and a control circuit 1102 solid-acrylic (polyacrylic acid methyl vinegar, PMMA) light-guided object ❹1103, a light-conducting object 11〇4. Among them, the surface of the solid acrylic light guiding object has a total reflection surface, the surface of the light-conducting object 1HH has a light-emitting surface, and the material of the light-conducting object 1104 can be glass, plastic, pc, acrylic (polymethyl) Acrylic acid, PMMA), Shiqi gum, liquid filling, colloidal filling or soft stone. In this implementation, the material of the light-conducting object 1UM (4) is soft. In general, as long as the light passes through the interface of the medium having different refractive indices, the light energy loss (hereinafter referred to as refractive index loss) is caused by the reverse sputtering, scattering, and the like. The difference in refractive index between the two ends of the interface is higher. The higher the loss of the lion rate, especially from the high-definition to the low-refractive-end end, even the total reflection of the stomach is the biggest fold. (4) The heart is broken. The refractive index of the light guiding object 11〇3 and the soft stone illuminating material 1104 is about the same (~15) 'The light self-illuminating diode light source _ does not pass any air (4) after injection), therefore, the solid PMMA light The guiding object Cong and the soft miscellaneous object can be regarded as a single-optical succession, and the refractive index loss of several light paths. However, when light is transmitted to the surface of the soft Shijiao light-conducting object 1104, the light enters the refractive index from the high refractive index end! The first refractive index loss is caused by the air (see Figure 12, 200934543 笫 12), and the second refractive index loss occurs when the air re-enters the tissue (n~14, as shown in Figure 4B) (see Figure 5). The total refractive index loss is the sum of the first refractive index loss plus the second refractive index loss. If the light-emitting surface of the soft silicone light-conducting material 11〇4 is directly in contact with the tissue, so that the soft silicone light-conducting material 11〇4 and the tissue ιι6 have no air enthalpy, there is only one refractive index loss (see 13th). Figure), and the primary refractive index loss is significantly lower than the loss of light from the soft silicone light-conducting article 11〇4 into the air and then from the air into the tissue 1106. 〇 However, some tissues, such as the skin surface, have fine lines. Between the soft silicone light-transmitting material 1104 and the tissue 1106, a slight air gap is bound to occur. To reduce this type of refractive index loss, a photo-media substance 11〇5 (for example, water, a transparent liquid or a more manageable gel or paste) can be applied to the surface of the tissue 1106. The fine air gap between the light-emitting surface of the glue-conducting object and the tissue further reduces the refractive index loss. According to the optical principle, the refractive index of the optical medium ιι〇5 最好 is preferably between the soft silicone light-conducting article 1104 and the tissue 1106, and has a value of about 1.33 to 1.55 (see Figure 14). In the presence of the optical medium substance 11〇5, the refractive index loss at a large angle can be greatly reduced, as shown in Fig. 15, so that the incidence unevenness due to the change in the surface topography of the tissue and the incident angle of the light source can be improved. Referring to Fig. 16, a third preferred embodiment of the apparatus for illuminating a photodynamic therapy (PDT) of the present invention is shown in Fig. 16. The irradiation apparatus of this embodiment is for irradiating a tissue to which a purple-type photo-sensitive agent or its precursor 1607 is applied. The illumination device of the embodiment 13 200934543 may include a light emitting diode light source 16〇1, a power supply and control circuit 1602, a solid acrylic light guiding object 1603, a mirror surface 16〇4, and a liquid filled capsule 1605. . In the present embodiment, the capsule is filled with a soft liquid as a light-conducting object, and its soft and elastic surface can be easily attached to the tissue 16 of the majority of the topography. And the conduit 165 1652 can be used to inject the cold and hot liquid into the capsule, so that the tissue 1606 of the treatment site can be cold and hot to reduce the pain or discomfort caused by the treatment. Please refer to FIG. 17 for a fourth preferred embodiment of the apparatus for illuminating a photodynamic therapy (PDT) of the present invention. The irradiation apparatus of this embodiment is for irradiating a tissue to which a purple-based photoreceptor or a precursor thereof is applied. The illumination device of this embodiment comprises a light emitting diode (LED) light source 1701, a power supply and control circuit 1702, a solid acrylic light guiding object 17〇3, a mirror surface 17〇4 and a vibration device 1705. Because it was found that the absorption of light in human tissues mainly comes from hemoglobin in the blood, and the 18th picture shows the absorption spectrum of each wavelength of human tissue (breast). As with most other tissues, it can be clearly seen that it is slightly larger than 4 The two strong absorption peaks near 〇〇nm and 55〇nm are completely consistent with the absorption characteristics of heme and aeroglobin in Fig. 19, and the strong absorption peak slightly larger than 400 nm is the soret band of heme. In the present embodiment, 'the solid acryl light guiding member 17 〇 3 is applied with an appropriate degree of pressure at the contact portion to easily remove the local blood in the tissue 1708 to reduce the absorption of hemoglobin by incident light', especially in Wavelength around 400 nm. When the pressure is released, the surrounding blood will flow back to supplement the oxygen required for photodynamic therapy. Repeating this process of oppression and release of pressure, like a pump, exchanges oxygen-rich 14 200934543 blood into the irradiation area, sustainable supplementation of oxygen consumed by photodynamic therapy. As shown in Fig. π, the vibration device of the present embodiment may be a piezoelectric element or an eccentric wheel, and the like. The Long Light Solution M6 transmits vibration to the tissue ‘ to reduce the discomfort during treatment, and to increase the probability of molecular collision due to vibration, and to enhance the effect of photodynamic therapy. In addition, the light-conducting article of the present embodiment has solid particles 1707 as a light-diffusing structure, and the solid particles 17〇7 〇 may be alumina (A1203), zinc oxide (Zn〇), anatase phase (3 she折 Fine e) Titanium dioxide (Τι02) and other materials are different from the light material reading, which can cause light scattering to achieve excellent illumination uniformity. Please refer to FIG. 20, which is a fifth preferred embodiment of the illumination device for photodynamic therapy (ph〇t〇dy_ic _, PDT) of the present invention. The actual illumination device is used to illuminate a tissue to which a purple-type photoreceptor or its precursor is applied. The illumination device of the embodiment comprises a light-emitting diode light source, a power supply and control circuit 2〇〇2, a mirror surface 2003, a light-conducting liquid container 2〇〇4, a solid particle 2〇〇5 and a light. Detector 2006. Among them, the light-conducting liquid container 2〇〇4 is filled with a light-conducting liquid 2007' and the light-conducting liquid 2〇〇7 is doped with solid particles 2〇〇5. Since the refractive index of the light-conducting liquid is greater than that of the air, the light is easily reflected back to the light-conducting liquid 2〇〇7, and by the scattering of the solid particles 2005, the light-conducting liquid 2〇〇7 is filled with light in all directions. The tissue 2008 is immersed in this liquid, and the position and angle can be uniformly irradiated with uniform I1, which is especially suitable for tissues with extremely uneven shape. The photodetector 2006 is coupled to the photoconductive liquid container 2〇〇4 for detecting the light output of the light conduction 15 200934543 liquid 2007, generating a detection signal to adjust the current, and also performing automatic light intensity control through the loop. 'Even or programmed light intensity control, so that the light exposure measurement can be fully grasped. If the light side detector 2006 has a wavelength detection function, it can be used to grasp the aging state of the light source and replace the light source in time. Regardless of any of the above-mentioned designs, the light-conducting object is easy to be separated from the electronic components such as the light-emitting diodes (for example, the light-objects can be separated from the other), so that only Part of the contact tissue is disinfected or discarded separately to avoid damage to the f-component during the operation. It is of course also possible to cover the surface of the light-transmissive article with a replaceable sheet or film to achieve the same effect. The above-mentioned real customs are only for the realization of the confession and method of wealth, and the concepts and methods can be used in conjunction with each other, and are not contrary to the disclosed embodiments. The above is only the preferred embodiment of the present invention, and all variations and modifications made by the application of the present invention should be within the scope of the present invention. [Simple description of the diagram] Figure 1 shows the photodynamic reaction procedure of a typical photo-sensitizer under light excitation. Figure 2A shows the relationship between the transmittance of human tissue (dashed line) and the ph〇t〇frin light-sensitive substance (solid line on the left of the figure) and the previous wavelength. The first twist diagram is the wavelength of light-sensitive substances used in photodynamic therapy and their conventional wavelengths. 16 200934543 Figure 3 shows the prior art illumination device. Figure 4A is a prior art illumination device. Figure 4B shows the refractive indices of tissues such as skin, muscles, and organs. ^ The picture shows the relationship between the light transmittance of light from the air and the human angle (9). Figure 6 is the first example of the present invention. The figure is a typical absorption spectrum of purple, and the strongest absorption peak around 4 〇〇 nm is its Soret Band. Figure 7B shows the wavelength of the strongest absorption peak (SoretBand) of some purple (mouth). Figure 8 shows the metabolic process of ALA-PpIX in tissues. The graph shows that the photoelectric conversion efficiency (external quantum efficiency) and wavelength distribution relationship of the commercially available gallium-indium gallium indium-based coffee makers are clearly seen to have the best luminous efficiency in the vicinity of 4〇5, and this range is compatible with most purpurin. The 380 lungs ~ 430nm SoretBand distribution overlap. The =10 figure shows the spectrum and ρρΐχ absorption spectrum of a typical 405 nm nitrided gallium indium LED. The φ 11 diagram is a schematic view of a second preferred embodiment of the present invention. = The graph shows the relationship between light (4), 5 through riding material _ shooting _ and human (four) degrees. The graph shows the relationship between the transmittance of light emitted from the inside of the η=1.5 transparent material to the W.4 structure and the angle of incidence. Figure 14 is a model for calculating the refractive index of the optical medium (8) for the total incident rate of the light energy. The light field of the chip LED chip uses the lambertian light field mode 1 light-conducting object and the refractive index of the tissue respectively. The figures are 1.5 and 1.4. The picture shows the refractive index of the model juice optical medium material W and the light-free medium substance (n U different degrees of human light energy difference, the light source of the towel source (LED_ehip) 17 200934543 field uses the lambertian light field The refractive index of the model, the light-conducting article and the tissue are assumed to be 1.5 and 1.4, respectively. Figure 16 is a schematic view of a third preferred embodiment of the present invention. Figure 17 is a view of a device according to a fourth preferred embodiment of the present invention. Figure 18 is a graph showing the absorption coefficient of each wavelength of the human breast. Fig. 19 is a graph showing the relationship between the absorption coefficient of human hemoglobin and the wavelength. Fig. 20 is a schematic view showing the fifth preferred embodiment of the present invention. Indium gallium indium (AlInGaN) light-emitting diode 601 power supply and control circuit 602, 1102, 1602, 1702, 2002 mirror 603, 1604, 1704, 2003 optical mirror 604 purple family light sensitive agent or its precursors 605, 1107 , 1607^ Organization 606, 1106, 1606, 1708, 2008 Light-emitting diodes 1101, 16 (H, 1701, 2001 solid acrylic light guiding object 1103, 1603, 1703 light-conducting object 1104, 1706 optical medium substance 1105 liquid-filled capsule 1605 tube Roads 1651, 1652 Solid particles 1707, 2005 Vibrating device 1705 18 200934543 Exclusion of blood direction 1709 Light-conducting liquid container 2004 Photodetector 2006 Light-conducting liquid 2007