200836792 九、發明說明 【發明所屬之技術領域】 本發明係關於荷電粒子線照射裝置，具備照射室，該 照射室具有可在被荷電粒子線照射的被照射體周圍旋轉之 ^ 荷電粒子線照射部。 * 【先前技術】 馨 先前，照射荷電粒子線之荷電粒子線照射裝置，已知 有例如照射質子線以治療腫瘤之質子線治療裝置。這種腫 瘤治療係配合腫瘤的形狀和位置，將絶對線量、線量分布 、照射位置等照射計畫予以立案，且必須依照此照射計畫 ^ ，以良好的精確度進行荷電粒子線之照射。對患者照射質 子線時，爲了避免照射到重要器官、腦幹、視神經、脊髓 等，照射位置之精確度特別重要。然後，適用於這種腫瘤 治療的質子線治療裝置，係藉由具備照射室（旋轉支架） • ，該照射室具有在患者周圍旋轉自如的質子線照射部，而 提高質子線照射部之移動自由度（例如，參照專利文獻1 )。 ^ 〔專利文獻1〕日本專利特開平1 1 一 47287號公報 【發明內容】 近年來，在用於照射荷電粒子線的荷電粒子線照射裝 置，被要求檢測所照射的荷電粒子線要照射在被照射體的 哪個位置。因此，開發出利用PET攝影機，藉由照射在被 200836792 * 二乂 一〜 * 照射體的荷電粒子線和被照射體内的原子核，檢測來自兩 者的核反應所產生之正電子放出核的消滅r射線，用以檢 測荷電粒子線之照射位置的技術。但是，該技術中，由於 pet攝影機被固定，只能確認特定部位之位置，因此被要 求確認所要部位之位置。 * 本發明係爲了解決這種課題而發明者，其目的在於提 供可確認在所要部位之照射位置的荷電粒子線照射裝置。 φ 根據本發明之荷電粒子線照射裝置，係具備照射室， 該照射室具有可在荷電粒子線所照射的被照射體周圍旋轉 的荷電粒子線照射部，其特徵爲：具備一對檢測部，係夾 持被照射體而配置在兩側，用於檢測在被照射體所產生的 消滅r射線，將荷電粒子線照射部的旋轉中心軸的延伸方 % 向當作X軸方向，檢測部可朝前述X軸方向移動。 ^ 根據如此地構成之荷電粒子線照射裝置，具備照射室 ，該照射室具有可在被照射體周圍旋轉的荷電粒子線照射 • 部，用於檢測被照射體所產生的消滅r射線之檢測部，係 設定成可朝荷電粒子線照射部旋轉中心軸延伸方向之X軸 方向移動。藉此，以使檢測部朝X軸方向移動的方式，可 防止檢測部妨礙荷電粒子線照射部之旋轉。且，將被照射 ' 體搬入、搬出照射室時，檢測部不會成爲阻礙。且，可確 認所要部位之位置。且，由於亦可配合被照射體之大小使 檢測部朝X軸方向移動，因此可擴大檢測部之檢測範圍。 此處，將檢測部設定成可在X軸周圍旋轉爲佳。藉此 ，檢測部可在被照射體周圍旋轉而提高檢測部移動自由度 -6- 200836792 _ _ -.,^ , - - - ，因此可利用小型化的檢測部（例如P E T攝影機）進fj照 射位置之3維測定。 且，檢測部係以追從荷電粒子線照射部的旋轉而進行 旋轉爲佳。藉此，可一面維持荷電粒子線照射部所照射的 * 荷電粒子線和檢測部之位置關係，一面進行計測照射位置。 ^ 且，檢測部係以和荷電粒子線照射部一體地旋轉爲佳 。藉此，可利用使荷電粒子線照射部旋轉的旋轉驅動部， φ 使檢測部旋轉，因此不須爲了使檢測部旋轉而另外設置旋 轉驅動部。 且，檢/測部係設定成可朝彼此接近的方向移動爲佳。 藉此，藉由使夾持被照射體而配置在兩側的檢測部朝彼此 接近的方向移動之方式，可使檢測部接近被照射體以進行 測定照射位置，使測定精確度提高。 ‘ 且，將X軸方向之正交方向當作Y軸方向，將檢測 部設定成可在Y軸周圍旋轉爲佳。藉此，進而提高檢測部 * 之移動自由度，由於可從各種方向進行測定照射位置，可 進而提高測定精確度。且，由於使檢測部在朝Y軸方向延 伸的預定之軸周圍旋轉而可改變檢測部位置，因此例如檢 ’ 測部爲縱長形狀時，藉由將檢測部的長方向沿X軸方向配 * 置的方式，可容易進行檢測部朝X軸方向之移動。 如此地根據本發明之荷電粒子線照射裝置，由於可使 檢測部朝X軸方向移動，因此可防止檢測部阻礙荷電粒子 線照射部之旋轉。且，將被照射體搬入、搬出照射室時， 檢測部不會成爲阻礙。且，由於亦可配合被照射體的大小 200836792 使檢測部朝χ軸方向移動，因此可確認所要部位中的照射 位置。 【實施方式】 ‘ 以下，參照第1圖〜第5圖説明根據本發明之荷電粒 k 子線照射裝置之較佳第1實施形態。此外，在圖式説明中 ，對相同或相當之要素賦予相同符號，省略重複説明。本 Φ 實施形態係針對將荷電粒子線照射裝置當作質子線治療裝 置的情形進行説明。 如第1圖〜第3圖所示，質子線治療裝置1 00係對患 者（被照射體）5 1體内的腫瘤（照射目標物）P，照射質 子線（荷電粒子線）之裝置。 該質子線治療裝置1 00具備質子線照射部（荷電粒子 ^ 線照射部）1，該質子線照射部係安裝在旋轉支架1 03 (照 射室），且可在治療台（載置台）105周圍旋轉。 # 該質子線照射部1係如第.3圖所示，具備照射控制部 1 7，用以控制依序排列在質子線的照射方向A、使質子線 射束依序通過而將射束整形之散射體5、脊形濾鏡部7、 ^ 精密降能器9、擋塊式準直儀1 1、快速注射1 3、多葉式準 ‘ 直儀1 5、裝置各部之驅動。 將當作質子線產生部之功能的迴旋加速器3所產生的 質子線，通過輸送裝置送入該質子線照射部1。然後，藉 由使被送入的細質子線，例如通過厚度數mm的鉛所構成 的散射體（射束擴大部）5的方式，在照射方向A的正交 -8- 200836792 方向保持擴散而擴大成寬度大的射束。 來自上述散射體5的質子線射束係對應患者5 1體内 的腫瘤P之厚度（照射方向A的長度），而入射到脊形濾 鏡部（峰値調整濾鏡部）7，該脊形濾鏡部係用於保持分 布在質子線的能量深度。該脊形濾鏡部7具有由以階梯狀 變化厚度之金屬棒並排成簾狀所構成的複數個濾鏡7a，該 等複數個濾鏡7a係藉由金屬棒之不同形狀而形成彼此質 子線不同的擴大布拉格峰（以下稱「SOBP」）。然後， 脊形濾鏡部7係藉由照射控制部1 7之控制而被驅動，且 具有將適當選自上述複數個濾鏡7a之中的濾鏡插入質子 線通過位置之機構。藉由該構成，脊形濾鏡部7可選擇性 地變更使質子線通過的濾鏡7a，而可調整質子線的SOBP 峰之寬度。 通過該脊形濾鏡部7的質子線，係配合治療對象亦即 患者體内5 1的腫瘤P之深度而調整射束能量，入射至用 於調整最大到達深度之精密降能器（射束能量調整部）9 。該精密降能器9係由例如2個形成楔型之相對向的聚丙 烯擋塊9 a、9 b所構成，利用，藉由由照射控制部17之控 制來調節上述擋塊9 a、9 b之重疊方式，可連續地變化質 子線通過邰分的厚度。質子線因配合通過的物質厚度而喪 失能量，改變在患者5 1體内到達的深度，因此可藉由調 節該精密降能器9，將質子線之SOBP位置配合在患者51 體内之腫瘤P深度方向（照射方向A)的位置。 通過該精密降能器9之質子線射束，係入射到用於將 -9- 200836792 質子線的平面形狀（從照射方向A所見之形狀）粗整形之 擋塊式準直儀1 1。後述之多葉式準直儀1 5以外，此處進 行擋塊式準直儀1 1所進行之整形，係爲了不在患者附近 產生擋塊式準直儀1 1造成的2次放射線。 通過該擋塊式準直儀1 1之質子線，係輸入到例如樹 脂製的不整形濾鏡亦即快速注射（補償濾鏡）1 3，針對腫 瘤P最大深度之斷面形狀和組織不均一性進行修正。該快 速注射1 3之形狀係依據腫瘤輪廓線、和例如從X射線CT 之資料所求出的周邊組織之電子密度而算出。藉由利用這 種快速注射1 3的方式，使質子線射束最遠部（最大到達 深度部分）的立體形狀配合腫瘤P的最大深度部分形狀而 被整形，因此可更提高對腫瘤P之線量集中性。 通過該快速注射1 3之質子線射束係入射到多葉式準 直儀（形狀可變準直儀）15。多葉式準直儀15係由黃銅 製的寬度數mm之具有多數梳齒之2個遮線部1 5 a、1 5b， 排列成在中心突抵上述梳齒前端所構成。然後，藉由照射 控制部17之控制，以遮線部15a、15b使多數之各上述梳 齒在長方向進退的方式，多葉式準直儀15可使質子線射 束通過的開口 15c之位置及形狀變化。 通過多葉式準直儀1 5之質子線射束，被擷取出對應 上述開口 1 5 c形狀之輪廓，因此多葉式準直儀1 5係以使 開口 1 5c形狀變化的方式，可取得入射之質子線射束的所 要平面位置及平面形狀。如此地在所要的平面位置被取得 所要的平面形狀之質子線射束，係當作治療用質子線而被 -10- 200836792 照射在患者5 1。然後，藉由一面使多葉式準直儀1 5的開 口 1 5c之平面位置及平面形狀變化，使照射域的位置順序 朝水平方向（照射方向A之正交方向）移動，一面反覆照 射的方式，在腫瘤P全體照射質子線射束。 再者，該1質子線照射部1具備線量監視器23，係監 視照射在照射域的照射線量之手段。線量監視器23係設 在精密降能器9和擋塊式準直儀1 1之間，偵知通過的質 子線之線量。線量監視器23係將偵知之線量傳送到照射 控制部1 7當作監視器訊號s 1，照射控制部1 7可根據監視 器訊號s 1而辨識照射在照射域之照射線量。 且，質子線治療裝置1〇〇設有用於取得患者51的X 射線透視影像之X射線攝影裝置（X射線透視影像取得手 段）。該X射線攝影裝置具備X射線產生器、檢測透射 患者5 1的X射線之X射線檢測器。該等X射線產生器及 X射線檢測器係固定在旋'轉支架1 0 3，可在患者5 1周圍旋 轉。本實施形態中，具備二個X射線產生器，該等X射 線產生裝置係配置在相差9 0度之位置。且，在相對向於 X射線產生器之位置，配置X射線檢測器。X射線攝影裝 置係根據由X射線檢測器所檢測到的資料，作成患者51 的X射線透視影像，而可檢測骨、金屬標記以測定患者 5 1之位置。 此處，質子線治療裝置100具備PET裝置31，該 PET裝置31具有一對PET攝影機（檢測器）3〇，係安裝 在旋轉支架1 0 3，且設定成可在治療台1 〇 5周圍旋轉。即 -11 - 200836792 ，PET攝影機30和安裝在旋轉支架i〇3之質子線照射部1 ，係設定成可一體地在X軸周圍旋轉。PET裝置3 1除了 PET攝影機3 0之外，具備不圖示之影像處理部、記錄部 、顯示部等。影像處理部係根據由PET攝影機3 0所取得 '之影像資訊，進行影像處理，產生PET影像。記錄部係記 _ 錄被產生之PET影像等。被產生之PET影像係藉由顯示 部而顯示。 φ 該PET攝影機30係配置在治療台1〇5上的患者51兩 側，用於檢測消滅r射線。具體而言，對患者5 1進行集 中在腫瘤P之放射性藥劑（例如，11C蛋氨酸）之投藥（ 注入），PET攝影機30係檢測自腫瘤P (放射性藥劑之到 達位置）產生的消滅r射線。PET裝置3 1係發揮當作照 射目標位置檢測手段之功能，該照射目標位置檢測手段係 根據PET攝影機3 0檢測消滅r射線的結果，檢測腫瘤P 之位置。 • 且，PET攝影機30可檢測來自正電子放出核之消滅 T射線，該正電子放出核係因照射在患者5 1的質子線之 入射質子核和腫瘤P内之原子核兩者之核反應所產生。再 ^ 者’ PET裝置3 1係發揮當作質子線（荷電粒子線）到達 位置檢測手段之功能，該質子線（荷電粒子線）到達位置 檢測手段係根據PET攝影機30檢測消滅7射線的結果， 檢測被照射的質子線實際在患者5 1體内之到達位置。即 ’ ΡΈΤ裝置3 i係利用治療時使用的質子線之入射質子核 和患者5 1體内中之原子核兩者的相互核反應，從體内中 -12- 200836792 所產生的正電子放出核種計測消滅r射線，測定各產生核 種之強度分布，藉此可檢測患者51體内之實際的質子線 到達位置。 PET攝影機30係如第4圖所示，可朝旋轉支架1〇3 的旋轉中心軸X (以下稱「X軸」）方向移動，且可朝與 X軸正交之Y軸方向移動。各自支撐一對PET攝影機30 的PET攝影機支撐部32具有：朝X軸方向延伸之支撐構 件3 3、沿著該支撐構件33朝乂軸方向移動之又軸方向移 動構件34、設在該X軸方向移動構件34之前端部34a朝 Y軸方向延伸之Y軸方向延伸構件3 5、沿著該Y軸方向 延伸構件35朝Y軸方向移動之Y軸方向移動構件36。然 後，PET攝影機30係固定在Y軸方向移動構件36，且配 置成其檢測面3 0a爲彼此相對向。 在支撐構件3 3形成有在Y軸方向朝外側伸出之伸出 部33a，該伸出部33a係固定在旋轉支架1〇3之框i〇3a( 參照第2圖）。支撐構件3 3係配置在旋轉支架103的背 面面板1 0 3 b背面側（圖示右側）。在支撐構件3 3及X軸 方向移動構件3 4，形成有用於導引X軸方向移動構件3 4 的移動方向之滑動導件3 8，X軸方向移動構件3 4係經由 滑動導件38被支撐成可在X軸方向移動。然後，X軸方 向移動構件34係藉由固定在支撐構件33之汽缸37而被 驅動，可在X軸方向往返移動。 在Y軸方向延伸構件35及Y軸方向移動構件36，如 第5圖所示設置有用於導引γ軸方向移動構件36的移動 -13- 200836792 方向之滑動導件3 9 ’ Y軸方向移動構件3 6係經由滑動 件39被支撐成可在Υ軸方向移動。然後，γ軸方向移 構件3 6係藉由固定在γ軸方向延伸構件3 5之電動機 而被驅動，可在Υ軸方向往返移動。 電動機40係配置成其輸出軸41朝X軸及Υ軸所 交之Ζ軸方向（第5圖中的上下方向）延伸。輸出軸 係經由耦合件42而連接在朝Ζ軸方向延伸的驅動軸43 驅動軸43係藉由一對軸承44，被支撐成可在Υ軸方向 伸構件3 5旋轉。驅動軸43的一對軸承44間設有齒輪 。且，在驅動軸43之與耦合件42相反側的端部，設置 制動器46及電位計47。 且，在Υ軸方向移動構件3 6，朝Υ軸方向形成有 合齒輪45之齒條48。然後，以旋轉驅動電動機40的方 ，藉由齒輪45及齒條48傳達驅動力，使Υ軸方向移動 件36朝Υ軸方向往返移動。藉此，可使PET攝影機 對患者51接近。以將PET攝影機30配置成接近患者的 式，提高消滅r射線之檢測精確度。 該PET攝影機30可藉由旋轉支架103的背面面 l〇3b而收納在背面側，計測時，藉由汽缸37驅動，且 置在患者5 1兩側。 且，質子線治療裝置1〇〇具有進行治療台105之位 調整的治療台位置控制部（載置台控制部）。然後，該 療台位置控制部係根據由PET裝置31所取得之PET影 、由X射線攝影裝置所取得之X射線透視影像，控制 導 動 40 正 41 〇 延 45 有 咬 式 構 30 方 板 配 置 治 像 治 -14-[Technical Field] The present invention relates to a charged particle beam irradiation apparatus including an irradiation chamber having a charged particle beam irradiation unit that is rotatable around an object to be irradiated by a charged particle beam. . * [Prior Art] Xin Previously, a charged particle beam irradiation device that irradiates a charged particle beam is known, for example, as a proton therapy device that irradiates a proton beam to treat a tumor. This tumor treatment is based on the shape and position of the tumor, and the irradiation plan such as the absolute line quantity, the line quantity distribution, and the irradiation position is set up, and the irradiation particle line must be irradiated with good precision according to the irradiation plan ^. When the patient is exposed to protons, the accuracy of the irradiation position is particularly important in order to avoid exposure to vital organs, brainstem, optic nerve, and spinal cord. Then, the proton therapy device suitable for the treatment of such tumors has an irradiation chamber (rotary support) that has a proton beam irradiation portion that is rotatable around the patient, thereby improving the freedom of movement of the proton beam irradiation portion. Degree (for example, refer to Patent Document 1). [Patent Document 1] Japanese Laid-Open Patent Publication No. Hei No. Hei. No. Hei. No. Hei. No. Hei. No. Hei. Hei. Which position of the illuminating body. Therefore, it has been developed to use a PET camera to detect the positron emission nucleus generated by the nuclear reaction from both by irradiating the charged particle beam of the irradiated body of 200836792*2乂** and the nucleus of the irradiated body. Ray, a technique used to detect the position of the charged particle beam. However, in this technique, since the pet camera is fixed and only the position of the specific portion can be confirmed, it is required to confirm the position of the desired portion. The present invention has been made in an effort to solve such a problem, and an object of the invention is to provide a charged particle beam irradiation apparatus capable of confirming an irradiation position at a desired portion. φ The charged particle beam irradiation apparatus according to the present invention includes an irradiation chamber having a charged particle beam irradiation unit that is rotatable around the object to be irradiated by the charged particle beam, and is characterized in that a pair of detection units are provided. The object to be irradiated is placed on both sides, and is used to detect the extinction r-ray generated by the object to be irradiated, and the % of the extension of the central axis of rotation of the charged particle beam irradiation unit is regarded as the X-axis direction, and the detecting portion can be Moves in the X-axis direction. ^ The charged particle beam irradiation apparatus configured as described above includes an irradiation chamber having a charged particle beam irradiation unit that is rotatable around the object to be irradiated, and a detection unit for detecting the r-ray generated by the object to be irradiated The movement is set so as to be movable in the X-axis direction in which the center axis of rotation of the charged particle beam irradiation unit is extended. Thereby, the detection unit can be prevented from interfering with the rotation of the charged particle beam irradiation unit so that the detection unit moves in the X-axis direction. Further, when the irradiated body is carried in and out of the irradiation chamber, the detecting portion does not become an obstacle. Also, confirm the location of the desired part. Further, since the detecting portion can be moved in the X-axis direction in accordance with the size of the irradiated body, the detection range of the detecting portion can be enlarged. Here, it is preferable to set the detecting portion so as to be rotatable around the X-axis. Thereby, the detecting unit can rotate around the object to be irradiated to improve the degree of freedom of movement of the detecting unit -6-200836792 _ _ -., ^ , - - - , so that it can be irradiated with fj by a small-sized detecting unit (for example, a PET camera). 3-dimensional measurement of position. Further, it is preferable that the detecting unit rotates in accordance with the rotation of the charged particle beam irradiation unit. Thereby, the irradiation position can be measured while maintaining the positional relationship between the charged particle beam and the detecting portion which are irradiated by the charged particle beam irradiation unit. Further, it is preferable that the detecting portion is integrally rotated with the charged particle beam irradiation portion. Thereby, the rotation drive unit that rotates the charged particle beam irradiation unit can be rotated, and the detection unit can be rotated. Therefore, it is not necessary to separately provide the rotation drive unit in order to rotate the detection unit. Further, it is preferable that the inspection/measurement section is set to be movable in a direction in which they approach each other. By moving the detecting portions disposed on both sides so as to move toward each other, the detecting portion can be brought close to the object to be irradiated to measure the irradiation position, and the measurement accuracy can be improved. ‘And, the orthogonal direction of the X-axis direction is taken as the Y-axis direction, and it is preferable to set the detection unit so that it can rotate around the Y-axis. Thereby, the degree of freedom of movement of the detecting unit* is further improved, and since the irradiation position can be measured from various directions, the measurement accuracy can be further improved. Further, since the detection unit can be rotated around the predetermined axis extending in the Y-axis direction to change the position of the detection unit, for example, when the detection unit has a vertically long shape, the longitudinal direction of the detection unit is aligned along the X-axis direction. * The setting method makes it easy to move the detection unit in the X-axis direction. According to the charged particle beam irradiation apparatus of the present invention, since the detection portion can be moved in the X-axis direction, it is possible to prevent the detection portion from blocking the rotation of the charged particle beam irradiation portion. Further, when the object to be irradiated is carried in and out of the irradiation chamber, the detecting portion does not become an obstacle. Further, since the detection unit can be moved in the x-axis direction in accordance with the size of the object to be irradiated 200836792, the irradiation position in the desired portion can be confirmed. [Embodiment] Hereinafter, a preferred first embodiment of a charged particle k-ray irradiation apparatus according to the present invention will be described with reference to Figs. 1 to 5 . In the description of the drawings, the same or corresponding elements are designated by the same reference numerals, and the repeated description is omitted. This Φ embodiment is directed to a case where the charged particle beam irradiation device is used as a proton therapy device. As shown in Fig. 1 to Fig. 3, the proton therapy device 100 is a device that irradiates a proton (charged particle beam) to a tumor (irradiation target) P in a patient (irradiated body) 51. The proton therapy device 100 includes a proton beam irradiation unit (charged particle irradiation unit) 1 attached to the rotating holder 103 (irradiation chamber) and surrounding the treatment table (mounting table) 105. Rotate. # The proton beam irradiation unit 1 includes an irradiation control unit 17 for controlling the irradiation direction A of the proton line in order, and sequentially passing the proton beam beam to shape the beam as shown in Fig. 3 The scatterer 5, the ridge filter section 7, the precision degrader 9, the block type collimator 1 1, the rapid injection 1 3, the multi-leaf quasi-finger 1 5, and the driving of each part of the apparatus. The proton line generated by the cyclotron 3 functioning as a proton generating unit is sent to the proton beam irradiating unit 1 by a transport device. Then, the fine sub-wires to be fed are diffused in the direction of the orthogonal -8-200836792 in the irradiation direction A by, for example, a scatterer (beam expanding portion) 5 composed of lead having a thickness of several mm. Expand into a beam with a large width. The proton beam beam from the scatterer 5 corresponds to the thickness (length of the irradiation direction A) of the tumor P in the body of the patient 51, and enters the ridge filter portion (peak 値 adjustment filter portion) 7, which is ridged. The shape filter section is used to maintain the energy depth distributed over the proton line. The ridge filter portion 7 has a plurality of filters 7a formed by a metal rod having a thickness varying in steps and arranged in a curtain shape. The plurality of filters 7a form protons by different shapes of the metal rods. The line expands the Prague peak (hereinafter referred to as "SOBP"). Then, the ridge filter portion 7 is driven by the control of the irradiation control unit 17, and has a mechanism for inserting a filter appropriately selected from the plurality of filters 7a into the proton line passing position. With this configuration, the ridge filter portion 7 can selectively change the width of the SOBP peak of the proton beam by selectively changing the filter 7a through which the proton beam passes. By the proton line of the ridge filter portion 7, the beam energy is adjusted in accordance with the depth of the tumor P in the patient's body, that is, the depth of the tumor P in the patient's body, and is incident on the precision energy reducer (beam) for adjusting the maximum depth of arrival. Energy adjustment unit) 9 . The precision degrader 9 is composed of, for example, two opposing polypropylene stoppers 9a, 9b forming a wedge shape, and the stoppers 9a, 9 are adjusted by the control of the irradiation control unit 17. The overlapping mode of b can continuously change the thickness of the proton line passing through the split. The proton line loses energy due to the thickness of the material passing through, changing the depth of arrival in the body of the patient 51. Therefore, by adjusting the precision energy reducer 9, the SOBP position of the proton line can be matched to the tumor P in the patient 51. The position in the depth direction (irradiation direction A). The proton beam beam passing through the precision degrader 9 is incident on a block type collimator 1 1 for rough shaping the planar shape of the proton line of -9-200836792 (the shape seen from the irradiation direction A). In addition to the multi-leaf collimator 15 described later, the shaping of the stopper type collimator 1 is performed here so that the secondary radiation caused by the stopper type collimator 1 1 is not generated in the vicinity of the patient. The proton line of the block type collimator 1 is input to, for example, a resin-made non-shaping filter, that is, a rapid injection (compensation filter) 13 for the cross-sectional shape and tissue unevenness of the maximum depth of the tumor P. Sexual corrections. The shape of the rapid injection 13 is calculated based on the tumor outline and the electron density of the surrounding tissue obtained, for example, from the X-ray CT data. By using such a rapid injection method, the three-dimensional shape of the farthest portion (maximum reaching depth portion) of the proton beam is shaped to match the shape of the maximum depth portion of the tumor P, thereby increasing the amount of line P to the tumor. Concentration. The proton beam beam passing through the rapid injection 13 is incident on a multi-leaf collimator (shape variable collimator) 15. The multi-leaf collimator 15 is composed of two shade portions 1 5 a and 15 b having a plurality of comb teeth and having a width of several mm, which are arranged in a brass shape, and are arranged so as to protrude toward the distal end of the comb teeth. Then, by the control of the irradiation control unit 17, the multi-leaf collimator 15 can pass the opening 15c through which the proton beam passes, so that the plurality of comb teeth are advanced and retracted in the longitudinal direction by the blind portions 15a and 15b. Position and shape changes. By the proton beam of the multi-leaf collimator 15 , the contour corresponding to the shape of the opening 15 c is extracted, so that the multi-leaf collimator 15 can be obtained by changing the shape of the opening 15 c. The desired planar position and planar shape of the incident proton beam. The proton beam beam having the desired planar shape obtained at the desired planar position is irradiated to the patient 51 by -10-200836792 as a therapeutic proton. Then, by changing the plane position and the planar shape of the opening 15c of the multi-leaf collimator 15 so that the position of the irradiation region is sequentially shifted in the horizontal direction (the orthogonal direction of the irradiation direction A), the irradiation is repeated. In the way, the whole of the tumor P illuminates the proton beam. Further, the one-plasma line irradiation unit 1 includes a line amount monitor 23, and is a means for monitoring the amount of irradiation line irradiated in the irradiation region. The line amount monitor 23 is provided between the precision degrader 9 and the block type collimator 1 1 to detect the amount of the line of the passing proton. The line amount monitor 23 transmits the detected line amount to the irradiation control unit 17 as the monitor signal s 1, and the irradiation control unit 17 recognizes the amount of the irradiation line irradiated in the irradiation field based on the monitor signal s1. Further, the proton beam therapy apparatus 1 is provided with an X-ray imaging apparatus (X-ray fluoroscopic image acquisition means) for acquiring an X-ray fluoroscopic image of the patient 51. This X-ray imaging apparatus includes an X-ray generator and an X-ray detector that detects X-rays transmitted through the patient 51. The X-ray generator and the X-ray detector are fixed to the rotary 'rotary holder 103, and are rotatable around the patient 51. In the present embodiment, two X-ray generators are provided, and the X-ray generating devices are disposed at positions that differ by 90 degrees. Further, an X-ray detector is disposed at a position opposite to the X-ray generator. The X-ray imaging apparatus creates an X-ray fluoroscopic image of the patient 51 based on the data detected by the X-ray detector, and detects bone and metal marks to determine the position of the patient 51. Here, the proton therapy device 100 is provided with a PET device 31 having a pair of PET cameras (detectors) 3 〇 mounted on the rotating stand 203 and set to be rotatable around the treatment table 1 〇 5 . That is, -11 - 200836792, the PET camera 30 and the proton beam irradiation unit 1 attached to the rotating stand i〇3 are set to be rotatable integrally around the X axis. The PET device 3 1 includes an image processing unit, a recording unit, a display unit, and the like, which are not shown, in addition to the PET camera 30. The image processing unit performs image processing based on the image information acquired by the PET camera 30 to generate a PET image. The recording department records _ recorded PET images and the like. The resulting PET image is displayed by the display portion. φ The PET camera 30 is disposed on both sides of the patient 51 on the treatment table 1〇5 for detecting the elimination of r rays. Specifically, the patient 51 is administered a drug (injection) of a radiopharmaceutical (e.g., 11C methionine) concentrated on the tumor P, and the PET camera 30 detects the extinct r-ray generated from the tumor P (the arrival position of the radiopharmaceutical). The PET apparatus 31 functions to function as an irradiation target position detecting means for detecting the position of the tumor P based on the result of detecting the extinction of the r-ray by the PET camera 30. • Further, the PET camera 30 can detect the extinct T-rays from the positron emission nucleus generated by the nuclear reaction of both the incident proton nucleus irradiated on the proton line of the patient 51 and the nucleus in the tumor P. Further, the 'PET device 3 1 functions as a proton line (charged particle line) reaching the position detecting means, and the proton line (charged particle line) arrival position detecting means detects the result of destroying the 7 ray according to the PET camera 30. The position at which the illuminated proton line actually reaches the body of the patient 51 is detected. That is, the ΡΈΤ device 3 i uses the mutual nuclear reaction between the incident proton nucleus of the proton line used in the treatment and the nucleus in the body of the patient, and the positron emission nucleus measurement from the body -12-200836792 is eliminated. The r-ray is used to measure the intensity distribution of each of the produced nuclear species, whereby the actual proton line arrival position in the patient 51 can be detected. As shown in Fig. 4, the PET camera 30 is movable in the direction of the central axis of rotation X (hereinafter referred to as "X-axis") of the rotary holder 1〇3, and is movable in the Y-axis direction orthogonal to the X-axis. The PET camera support portion 32 each supporting a pair of PET cameras 30 has a support member 33 extending in the X-axis direction, a further axial direction moving member 34 moving in the z-axis direction along the support member 33, and being disposed on the X-axis The Y-axis direction extending member 35 extending in the Y-axis direction of the front end portion 34a of the direction moving member 34 and the Y-axis direction moving member 36 moving in the Y-axis direction along the Y-axis direction extending member 35. Then, the PET camera 30 is fixed to the Y-axis direction moving member 36, and is disposed such that the detecting faces 30a thereof face each other. The support member 33 is formed with a projecting portion 33a projecting outward in the Y-axis direction, and the projecting portion 33a is fixed to the frame i〇3a of the swivel bracket 1〇3 (refer to Fig. 2). The support member 3 3 is disposed on the back side (the right side of the drawing) of the back panel 1 0 3 b of the rotary holder 103. In the support member 33 and the X-axis direction moving member 34, a slide guide 3 for guiding the moving direction of the X-axis direction moving member 34 is formed, and the X-axis direction moving member 34 is guided via the slide guide 38. The support is movable in the X-axis direction. Then, the X-axis direction moving member 34 is driven by the cylinder 37 fixed to the support member 33, and is reciprocally movable in the X-axis direction. In the Y-axis direction extending member 35 and the Y-axis direction moving member 36, as shown in Fig. 5, a sliding guide for moving the γ-axis direction moving member 36 in the direction of the -13,360,792 direction is provided. The member 36 is supported via the slider 39 to be movable in the z-axis direction. Then, the γ-axis direction shifting member 36 is driven by the motor fixed to the γ-axis direction extending member 35, and is reciprocally movable in the x-axis direction. The motor 40 is disposed such that its output shaft 41 extends in the x-axis direction (vertical direction in Fig. 5) where the X-axis and the x-axis intersect. The output shaft is coupled to the drive shaft 43 extending in the x-axis direction via the coupling member 42. The drive shaft 43 is supported by the pair of bearings 44 so as to be rotatable in the x-axis extending member 35. A gear is provided between the pair of bearings 44 of the drive shaft 43. Further, a stopper 46 and a potentiometer 47 are provided at an end of the drive shaft 43 opposite to the coupling member 42. Further, in the z-axis direction moving member 36, the rack 48 of the gear 45 is formed in the z-axis direction. Then, the driving force is transmitted by the gear 45 and the rack 48 to rotationally drive the motor 40, and the z-axis moving member 36 is reciprocated in the z-axis direction. Thereby, the PET camera can be brought close to the patient 51. In order to configure the PET camera 30 to be close to the patient, the detection accuracy of eliminating the r-ray is improved. The PET camera 30 can be housed on the back side by the back surface l〇3b of the rotary holder 103, and is driven by the cylinder 37 at the time of measurement, and placed on both sides of the patient 51. Further, the proton therapy device 1A has a treatment table position control unit (mounting table control unit) that adjusts the position of the treatment table 105. Then, the treatment table position control unit controls the guide 40 by 41 based on the PET image acquired by the PET device 31 and the X-ray fluoroscopic image acquired by the X-ray imaging device. Governance like rule-14-
200836792 療台105之位置，且調整治療台1〇5之位置，丨 射在治療台1 0 5上的患者5 1之腫瘤P。 照射控制部1 7係一面參照儲存在根據患者 P立體形狀所作成之腫瘤圖（目標物圖）1 9的: 特別是控制脊形濾鏡部7、精密降能器9、及多 儀1 5的動作。且，在此處將預先準備的快速注！ 在預定位置，使照射域最遠部的形狀對應腫瘤最 分複雜的形狀而被整形。 再者，照射控制部1 7係配合由PET裝置戶/ 質子線到達位置，進行質子線射束調整。即，照 1 7係控制脊形濾鏡部7、精密降能器9、及多葉 1 5的動作，調整質子線射束，使患者5 1體内的 際到達位置和腫瘤P之位置爲一致。 接著，説明關於使用如此地構成之質子線 1 〇〇之質子線照射方法（荷電粒子線照射方法） 不使用質子線治療裝置1〇〇時’ PET攝影| 於收納在背面面板1 〇3b背面側之狀態。此處· 關於對腦腫瘤患者之質子線治療。首先’使患考 旋轉支架1 〇 3内的治療台1 0 5上。患者5 1的長 置成沿X軸方向。接著，等候對患者51進行1 投藥（S1 )、對腦腫瘤聚集MC蛋氨酸（S2)。 由PET攝影機3 0測定聚集在腦腫瘤之11 C蛋_ 的消滅r射線（第1檢測步驟、S3)。此時， 37，使PET攝影機30朝X軸方向移動而配置 :質子線照 5 1的腫瘤 :訊，一面 •葉式準直 时13設置 :大深度部 :檢測到的 :射控制部 :式準直儀 丨質子線實 治療裝置 〇 I 3 0係處 =一例説明 :5 1躺在 t方向係配 i蛋氨酸 接著，藉 ^酸所放出 驅動汽缸 在患者5 1 -15- 200836792 兩側’驅動電動機40使PET攝影機30朝Y軸方向移動 ’調節PET攝影機3 0彼此的間隔。進行3維影像測定時 ’使旋轉支架！ 〇3旋轉，進行消滅r射線之計測。 接著，根據PET攝影機30測定的結果，作成PET影 像’檢測腦腫瘤位置（照射目標位置檢測步驟、S4 )。接 著1 ’藉由X射線攝影裝置進行透視攝影，作成患者51的 X Ιί，線影像（X射線透視影像取得步驟），確認骨及金屬 φ 標記位置。此外，亦可改變ΡΕΊΓ攝影及X射線攝影之順 序’亦可交替進行複數次攝影。且，配合必要使旋轉支架 1 03旋轉’改變X射線產生器、χ射線檢測器之位置。 接著，根據PET影像和X射線影像，將照射計畫立 ^ 案（S6 )。此處，照射計畫係決定例如：絶對線量、線量 分布、患者5 1之位置等。接著，根據已決定之照射計畫 ’進行治療台105之位置調整（載置台位置調整步驟、S7 )’將患者51配置在適當位置。 • 接著，依循已決定之照射計畫進行射束調整，配合必 要使旋轉支架1 03旋轉，變更質子線照射部1之位置，朝 腫瘤照射1次質子線（S8 )。然後，藉由PET攝影機30 ' ’測定來自照射的質子線和患者5 1體内的原子核兩者之 核反應所產生之正電子放出核的消滅r射線（第2檢測步 驟、S9)。此時，使PET攝影機30彼此以互相接近的方 式在Y軸方向移動，使PET攝影機30接近患者51，進行 消滅7射線之檢測。且，亦可使PET攝影機30旋轉，進 行測定。接著，根據PET攝影機30測定的結果，作成 -16- 200836792 PET影像，檢測患者51體内之質子線到達位置，確 際照射域（荷電粒子線到達位置檢測步驟、S 1 0 )。 接著，比較被照射的質子線實際到達患者51體 位置、照射計畫之照射目標位置（腫瘤位置），有位 ' 移的情況時’進行射束調整使質子線照射在照射目標 ' 之容許範圍内（射束調整步驟、S 1 1 )。射束調整終 ，照射質子線（s 1 2 )。此外，亦可再度實施S 8〜S 1 1 φ 根據這種質子線治療裝置100，可將？飞1^攝影擔 設在旋轉支架1 03 ’藉由該PET攝影機3 0，計測被照 質子線的入射質子核和腫瘤内的原子核兩者之核反應 生的正電子放出核之消滅7射線，因此可確認被照射 子線的實際到達位置。即，治療中可一面照射質子線 面檢測質子線到達位置。且，由於將PET攝影機3 0 ^ 在旋轉支架103，因此可配合旋轉支架103之旋轉 PET攝影機30在患者51周圍旋轉，照射質子線之後 • 進行消滅r射線之測定。且，可提高PET攝影機30 動自由度，並使用小型化之PET攝影機3 0進行3維 ，亦不須另外設置PET攝影機30用的旋轉驅動部。 ’ 由於PET攝影機30和質子線照射部1同步旋轉，因 一面維持PET攝影機30和質子線照射部1之旋轉方 的位置關係，一面進行消滅r射線之檢測。 且，PET攝影機30可朝X軸方向移動，且可被 在旋轉支架1 03的背面面板1 03b背面側。如此地使 攝影機30朝X軸方向移動之方式，可擴大PET攝影彳 認實 内之 置偏 位置 了後 〇 1 3 0 射之 所產 之質 ， -- 固定 ，使 隨即 之移 測定 且， 此可 向中 收納 PET 1 3 0 -17- 200836792 之檢測範圍。且，藉由pET攝影機3 0適當移 使PET攝影機30不會妨礙質子線照射部1之 ，將患者5 1搬入、搬出旋轉支架1 03内時， 3 0不會造成妨礙。且，亦可配合被照射體的 PET攝影機3 0，因此容易確認所要部位之照射 且，P E T攝影機3 0可朝夾住患者5 1的方 向）移動，由於可任意改變PET攝影機30間 此藉由使PET攝影機30在Y軸方向接近患考 ，可提高消滅r射線之檢測精確度。 且先前，例如腦腫瘤之放射線治療中，因 確度實現患者之定位，爲了使用固定具將患者 ，對患者造成很大的負擔。本發明之質子線照 子線照射方法中，在照射室内，可使患者5 1 台105的狀態下，使用PET攝影機30進行腫 ，而可修正腫瘤位置和實際被照射之質子線到 置偏移，將患者51定位在適當位置。藉此， 精確度進行患者之定位，而可謀求簡化患者之 患者的負擔。 接著，.一面參照第7圖及第8圖，説明 實施形態所相關之質子線治療裝置。該第2實 子線治療裝置和第1實施形態之質子線治療裝 異處，係第2實施形態之PET攝影機60進而 圍旋轉之處，及PET攝影機60之檢測面60& 處。 動之方式， 旋轉。再者 ΡΈΤ攝影機 大小而移動 位置。 向（Y軸方 的距離，因 f 5 1的方式 爲須以高精 的頭部固定 射裝置及質 於躺在治療 瘤位置確認 達位置之位 由於可以高 固定，減輕 :發明之第2 施形態之質 置1 0 0的相 可在Y軸周 形狀不同之 -18- 200836792 支撐PET攝影機60的PET攝影機支撐部61具備 影機固定部62，係用於將PET攝影機60固定在γ軸方 移動構件3 6内側的端部3 6 a。該攝影機固定部6 2安裝 用於旋轉驅動PET攝影機60之電動機63。該電動機 之輸出軸64係沿Y軸方向配置。然後，電動機63之輸 軸64連接著PET攝影機60，可在Y軸周圍旋轉。 PET攝影機60之撿測面60a係彎曲成圓弧狀，一 檢測面60a係配置成彼此相對向。PET攝影機60在收 時及朝X軸方向移動時，係配置成其長方向沿X軸方 (第7圖所示狀態）。且，計測7射線時，PET攝影機 係配置成圓弧之中心軸與X軸方向呈平行。此外，亦可 不與X軸方向呈平行之位置使PET攝影機60停止旋轉 而從各種角度進行測定。 如此地構成亦可獲得與第1實施形態之質子線治療 置1〇〇相同的效果，此外因爲PET攝影機60可在丫軸 圍旋轉，因此更加提高PET攝影機60之移動自由度， 可從各種方向進行照射位置之測定而謀求提高測定精確 〇 本發明並非受限定於上述第1實施形態及第2實施 態（以下稱「上述實施形態」）者。上述實施形態中 PET攝影機被設定成可在X軸周圍旋轉，但亦可是不在 軸周圍旋轉之構成，亦可是朝其他方向旋轉之構成。且 PET攝影機被構成可朝彼此接近的方向移動，但亦可 PET攝影機不朝彼此接近的方向移動之構成。且，雖然 攝 向 有 63 出 對 納 向 60 在 裝 周 而 度 形 X j 是 是 -19- 200836792 使用汽缸、電動機使PET攝影機移動，但亦可是使用油壓 缸、直線電動機等其他驅動裝置使PET攝影機移動。且， PET攝影機朝X軸方向之移動、朝γ軸方向之移動可以不 是直線狀移動，亦可是曲線狀、圓弧狀移動。 且，上述實施形態中，PET攝影機係安裝在旋轉支架 ’可和質子線照射部一體地在X軸周圍旋轉，但PET攝 影機亦可不和旋轉支架及質子線照射部一體地旋轉。例如 ，另外設置用於旋轉驅動PET攝影機之驅動裝置，使PET 攝影機以追從旋轉支架及質子線照射部的旋轉之方式進行 旋轉亦可，使PET攝影機以與旋轉支架及質子線照射部的 旋轉無關地進行旋轉亦可。 且，上述實施形態中，具備X射線裝置，實施X射 線攝影，但亦可省略X射線攝影。且，上述實施形態中， 放射性藥劑係蛋氨酸，但配合照射目標物而使用其他放射 性藥劑亦可。且，上述實施形態中，在照射室實施使用放 射性藥劑之PET檢査，但亦可使用在其他場所實施的資料 ’進行被照射體之定位。且，上述實施形態係對腦腫瘤進 行説明，但亦適用於其他腫瘤。 且，上述實施形態中，本發明係使用在照射質子線之 質子線照射裝置，但本發明亦可使用在碳射線照射裝置等 其他荷電粒子線照射裝置。 【圖式簡單說明】 第1圖係表示本發明之第1實施形態所相關之質子線 -20- 200836792 治療裝置之立體圖。 第2圖係第1圖所示之質子線治療裝置之剖視圖。 第3圖係構成第1圖中的質子線治療部之各要素之示 意圖。 第4圖係表示第1圖中的PET攝影機及PET攝影機 支撐部之俯視圖。 第5圖係第4圖之V-V箭頭方向視圖。 第6圖係表示本發明之實施形態所相關之質子線照射 方法的步驟之流程圖。 第7圖係表示本發明之第2實施形態所相關之質子線 治療裝置的PET攝影機及PET攝影機支撐部之俯視圖。 第8圖係第7圖VIII— VIII箭頭方向視圖。 【主要元件符號說明】 1 :質子線照射部（荷電粒子線照射部） 1 7 :照射控制部 30 : PET攝影機（檢測部） 5 1 :患者（被照射體） 100 :質子線治療裝置 1〇3 :旋轉支架（照射室） 1〇5 :治療台（載置台） P :腫瘤（照射目標物） X : X軸方向 Y : Y軸方向 -21 -200836792 The position of the treatment table 105, and adjust the position of the treatment table 1〇5, and the tumor P of the patient 5 1 on the treatment station 105. The irradiation control unit 17 refers to the tumor map (target map) 19 that is stored in accordance with the three-dimensional shape of the patient P: in particular, the control ridge filter portion 7, the precision energy reducer 9, and the multi-meter 15 Actions. And, here is a quick note prepared in advance! At a predetermined position, the shape of the farthest portion of the irradiation field is shaped corresponding to the most complicated shape of the tumor. Further, the illumination control unit 17 adjusts the position of the PET device/proton line to perform proton beam adjustment. In other words, the operation of the ridge filter unit 7, the precision degrader 9, and the multi-leaf 15 is controlled in accordance with the seventh system, and the proton beam is adjusted so that the position of the patient 5 1 and the position of the tumor P are Consistent. Next, a description will be given of a proton beam irradiation method using the proton beam 1 如此 configured as described above (charged particle beam irradiation method). When the proton beam treatment apparatus 1 is not used, 'PET photography| is stored on the back side of the back panel 1 〇 3b. State. Here · About proton therapy for patients with brain tumors. First, let the patient sit on the treatment table 1 0 5 in the rotating bracket 1 〇 3 . The length of the patient 51 is along the X-axis direction. Next, it is waited for 1 administration of the patient 51 (S1), and aggregation of MC methionine (S2) to the brain tumor. The extinction r-ray of the 11 C egg _ accumulated in the brain tumor was measured by the PET camera 30 (first detection step, S3). At this time, 37, the PET camera 30 is moved in the X-axis direction, and the proton line 5: tumor is detected: one side and the leaf type is collimated 13 is set: large depth portion: detected: shot control unit: Collimator 丨 proton line treatment device 〇I 3 0 Department = an example Description: 5 1 lying in the t direction tied with i methionine, followed by the acid release of the drive cylinder on both sides of the patient 5 1 -15- 200836792 'drive The motor 40 moves the PET camera 30 in the Y-axis direction to adjust the interval between the PET cameras 30. When performing 3D image measurement ‘Make rotating bracket! 〇3 rotates to perform the measurement of eliminating r-rays. Next, based on the result of measurement by the PET camera 30, a PET image is created to detect a brain tumor position (irradiation target position detecting step, S4). Next, a fluoroscopic photograph is taken by the X-ray apparatus to create an X Ι ,, line image (X-ray fluoroscopic image acquisition step) of the patient 51, and the position of the bone and the metal φ mark is confirmed. In addition, it is also possible to change the order of photography and X-ray photography, or to perform multiple photography alternately. Further, the rotation of the rotating bracket 103 is made necessary to change the position of the X-ray generator and the X-ray detector. Next, the irradiation plan is established based on the PET image and the X-ray image (S6). Here, the illumination plan determines, for example, the absolute line amount, the line amount distribution, the position of the patient 51, and the like. Next, the patient 51 is placed at an appropriate position based on the determined irradiation plan 'the position adjustment of the treatment table 105 (the stage setting adjustment step, S7). • Next, the beam adjustment is performed in accordance with the determined irradiation plan, and the rotation of the rotary holder 103 is necessary to change the position of the proton beam irradiation unit 1, and the proton line is irradiated once to the tumor (S8). Then, the extrinsic r-ray of the positron emitting nucleus generated by the nuclear reaction between the irradiated proton line and the atomic nuclei in the patient 51 is measured by the PET camera 30'' (second detecting step, S9). At this time, the PET cameras 30 are moved in the Y-axis direction in such a manner as to approach each other, and the PET camera 30 is brought close to the patient 51 to detect the 7-rays. Further, the PET camera 30 can be rotated to perform measurement. Next, based on the result of measurement by the PET camera 30, a PET image of -16-200836792 is prepared, and the proton line arrival position in the patient 51 is detected, and the irradiation field is confirmed (the charged particle beam arrival position detecting step, S 1 0 ). Next, it is compared that the irradiated proton line actually reaches the body position of the patient 51, the irradiation target position (tumor position) of the irradiation plan, and when there is a bit shift, the beam adjustment is performed so that the proton beam is irradiated to the allowable range of the irradiation target. Inside (beam adjustment step, S 1 1 ). At the end of the beam adjustment, the proton beam (s 1 2 ) is illuminated. In addition, it is also possible to implement S 8 to S 1 1 φ again according to the proton therapy device 100. Flying 1 ^ photography is carried on the rotating support 103 ' by the PET camera 30, measuring the positron emission nucleus of the nucleus of the incident proton nucleus of the illuminated proton and the nucleus of the tumor, destroying 7 rays, therefore The actual arrival position of the illuminated sub-line can be confirmed. That is, during the treatment, the proton line can be irradiated while detecting the proton line arrival position. Further, since the PET camera 300 is rotated on the holder 103, the PET camera 30 can be rotated around the patient 51 in conjunction with the rotation of the rotary holder 103 to illuminate the proton line. Further, the degree of freedom of movement of the PET camera 30 can be increased, and the miniaturized PET camera 30 can be used for three-dimensional, and the rotary driving unit for the PET camera 30 is not required to be separately provided. When the PET camera 30 and the proton beam irradiation unit 1 rotate in synchronization, the positional relationship between the rotation of the PET camera 30 and the proton beam irradiation unit 1 is maintained, and the detection of the extinction of the r-ray is performed. Further, the PET camera 30 is movable in the X-axis direction and can be on the back side of the back panel 103b of the swivel bracket 103. By moving the camera 30 in the X-axis direction as described above, it is possible to enlarge the position of the offset position in the PET photographing frame, and to produce the quality of the shot, and to fix it, and to measure it immediately. The detection range of PET 1 3 -17-200836792 can be accommodated in the middle. Further, when the PET camera 30 is appropriately moved by the pET camera 30 without interfering with the proton beam irradiation unit 1, when the patient 51 is carried in and out of the rotary holder 103, 30 does not interfere. Further, since the PET camera 30 of the object to be irradiated can be blended, it is easy to confirm the irradiation of the desired portion, and the PET camera 30 can move in the direction in which the patient 51 is sandwiched, since the PET camera 30 can be arbitrarily changed. By bringing the PET camera 30 closer to the test in the Y-axis direction, the detection accuracy of eliminating the r-ray can be improved. And in the past, for example, in the radiotherapy of brain tumors, the positioning of the patient is achieved by the degree of accuracy, and the patient is placed in a large burden in order to use the fixture. In the proton beam irradiation sub-ray irradiation method of the present invention, in the irradiation room, the PET camera 30 can be swollen in a state of the patient 51, and the tumor position and the actually irradiated proton line can be corrected to be offset. Position patient 51 in place. Thereby, the patient can be positioned with accuracy, and the burden on the patient can be simplified. Next, a proton therapy device according to an embodiment will be described with reference to Figs. 7 and 8. The second virtual line therapy device and the proton therapy device of the first embodiment are in the same manner as the PET camera 60 of the second embodiment, and the detection surface 60 & of the PET camera 60. Move the way, rotate. In addition, the camera moves in size and moves. The distance to the (Y-axis) is due to the fact that the f 5 1 method is required to be fixed with a high-precision head and the position of the patient is located at the position of the treatment tumor. The phase of the form is set to be different from the Y-axis shape. -18-200836792 The PET camera support portion 61 supporting the PET camera 60 is provided with a camera fixing portion 62 for fixing the PET camera 60 to the γ-axis. The end portion 3 6 a of the inner side of the moving member 36. The camera fixing portion 62 is mounted with a motor 63 for rotationally driving the PET camera 60. The output shaft 64 of the motor is disposed along the Y-axis direction. Then, the shaft of the motor 63 is disposed. 64 is connected to the PET camera 60 and rotatable around the Y-axis. The measurement surface 60a of the PET camera 60 is curved in an arc shape, and a detection surface 60a is disposed to face each other. The PET camera 60 is in the time of receiving and facing the X-axis. When the direction is moved, the long axis is arranged along the X-axis (state shown in Fig. 7). When measuring 7 rays, the PET camera is arranged such that the central axis of the arc is parallel to the X-axis direction. Can be taken in parallel with the X-axis direction The machine 60 is rotated and measured from various angles. In this configuration, the same effect as the proton therapy of the first embodiment can be obtained, and since the PET camera 60 can be rotated around the crucible, the PET is further improved. The degree of freedom of movement of the camera 60 can be measured by measuring the irradiation position in various directions, and the measurement accuracy is improved. The present invention is not limited to the first embodiment and the second embodiment (hereinafter referred to as "the above embodiment"). In the embodiment, the PET camera is set to be rotatable around the X-axis, but may be configured not to rotate around the shaft, or may be configured to rotate in other directions. The PET camera may be configured to move in a direction close to each other, but may be The PET camera does not move in the direction of approaching each other. Moreover, although the camera has 63 out of the right direction, 60 is in the shape of the circumference. X j is -19-200836792. The cylinder and motor are used to move the PET camera, but it can also be The PET camera is moved by using other driving devices such as a hydraulic cylinder or a linear motor. Moreover, the PET camera is oriented in the X-axis direction. The movement in the γ-axis direction may not be linear, or may be a curved or arc-shaped movement. Further, in the above embodiment, the PET camera is attached to the rotary holder and can be integrally formed with the proton beam irradiation unit on the X-axis. Rotating around, but the PET camera may not rotate integrally with the rotating bracket and the proton beam irradiation unit. For example, a driving device for rotationally driving the PET camera is additionally provided, so that the PET camera follows the rotation of the rotating bracket and the proton beam irradiation portion. Alternatively, the PET camera may be rotated regardless of the rotation of the rotating holder and the proton beam irradiation unit. Further, in the above embodiment, the X-ray apparatus is provided and X-ray imaging is performed, but X-ray imaging may be omitted. Further, in the above embodiment, the radioactive agent is methionine, but other radioactive agents may be used in combination with the irradiation target. Further, in the above embodiment, the PET inspection using the radioactive agent is performed in the irradiation chamber, but the irradiation of the object to be irradiated may be performed using the material carried out in another place. Further, the above embodiment describes a brain tumor, but is also applicable to other tumors. Further, in the above embodiment, the proton beam irradiation device for irradiating the proton beam is used in the present invention, but the present invention may be applied to other charged particle beam irradiation devices such as a carbon beam irradiation device. BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 is a perspective view showing a proton beam -20-200836792 therapeutic apparatus according to a first embodiment of the present invention. Figure 2 is a cross-sectional view of the proton therapy device shown in Figure 1. Fig. 3 is a schematic view showing the components constituting the proton therapy unit in Fig. 1. Fig. 4 is a plan view showing the PET camera and the PET camera support portion in Fig. 1; Figure 5 is a view of the direction of the arrow V-V of Figure 4. Fig. 6 is a flow chart showing the steps of the proton beam irradiation method according to the embodiment of the present invention. Fig. 7 is a plan view showing a PET camera and a PET camera support portion of the proton therapy device according to the second embodiment of the present invention. Figure 8 is a view of the arrow direction of Figure VIII-VIII of Figure 7. [Description of main component symbols] 1 : Proton beam irradiation unit (charged particle beam irradiation unit) 1 7 : Irradiation control unit 30 : PET camera (detection unit) 5 1 : Patient (illuminated body) 100 : Proton therapy device 1〇 3 : Rotating stand (irradiation room) 1〇5 : Treatment table (mounting table) P : Tumor (irradiation target) X : X-axis direction Y : Y-axis direction - 21 -