1352605 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】 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 提局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11— 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P E T攝影機，藉由照射在被 1352605 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τ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。 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7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- 1352605 ，因此可利用小型化的檢測部（例如PET攝影機）進行照 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， 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 1352605 使檢測部朝χ軸方向移動，因此可確認所要部位中 位置。 【實施方式】 以下，參照第1圖〜第5圖説明根據本發明之 子線照射裝置之較佳第1實施形態。此外，在圖式 . ，對相同或相當之要素賦予相同符號，省略重複説 • 實施形態係針對將荷電粒子線照射裝置當作質子線 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 〇〇 者（被照射體）5 1體内的腫瘤（照射目標物）p， 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 線照射部）1 ’該質子線照射部係安裝在旋轉支架1 射室），且可在治療台（載置台）105周圍旋轉。 Φ 該質子線照射部1係如第3圖所示，具備照射 1 7，用以控制依序排列在質子線的照射方向A、使 射束依序通過而將射束整形之散射體5、脊形濾鏡 精密降能器9、擋塊式準直儀1 1、快速注射1 3、多 直儀15、裝置各部之驅動。[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] Conventionally, 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 charged particle beam must be irradiated with good precision according to the irradiation plan. When the patient is irradiated with protons, it is particularly important to avoid the exposure to important organs, brainstem, optic nerve, spinal cord, etc. Then, the proton therapy device suitable for the treatment of such a tumor is provided with an irradiation chamber (rotary stent) which has a proton beam irradiation portion that is rotatable around the patient, and the movement of the proton beam irradiation portion is free. In the recent years, in a charged particle beam irradiation apparatus for irradiating a charged particle beam, it is required to detect the irradiation. [Patent Document 1] [Patent Document 1] [Patent Document 1] Japanese Patent Laid-Open No. Hei 11-47287. The position of the charged particle beam to be illuminated on the irradiated body. Therefore, it has been developed to detect the charge by detecting the charge of the positron emitting nucleus generated by the nuclear reaction of the two by irradiating the charged particle beam irradiated by the 1352605 and the nuclei irradiated in the body by the PET camera. The technique of the position of the particle line. 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. According to the charged particle beam irradiation apparatus of the present invention, there is provided an irradiation chamber having a charged particle beam irradiation unit that is rotatable around an object to be irradiated by a charged particle beam, and is characterized in that: a pair of detection units are provided The illuminating body is sandwiched and disposed on both sides, and is used for detecting the 7-ray ray generated by the object to be irradiated, and the extending direction of the central axis of rotation of the charged particle beam irradiation unit is taken as the X-axis direction, and the detecting portion can face the X Move in the direction of the axis. According to the charged particle beam irradiation apparatus configured as described above, the irradiation chamber has a charged particle beam irradiation unit that is rotatable around the object to be irradiated, and detects a detection unit that destroys the r-ray generated by the object to be irradiated. It is set to be movable in the X-axis direction in the 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. As a result, the detecting unit can rotate around the object to be irradiated to increase the degree of freedom of movement of the detecting unit -6 - 1352605. Therefore, the three-dimensional measurement of the irradiation position can be performed by a small-sized detecting unit (for example, a PET camera). 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. As a result, the rotation driving unit that rotates the charged particle beam irradiation unit can rotate the detection unit. 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 portion 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. Further, the orthogonal direction of the X-axis direction is referred to as the Y-axis direction, and it is preferable to set the detecting portion so as to be rotatable around the Y-axis. Thereby, the degree of freedom of movement of the detecting portion is further improved, and since the irradiation position can be measured from various directions, the measurement accuracy can be further improved. In addition, since the position of the detecting portion can be changed by rotating the detecting portion around a predetermined axis extending in the Y-axis direction, for example, when the detecting portion has a vertically long shape, the longitudinal direction of the detecting portion is arranged in the X-axis direction. The movement of the detecting portion in the X-axis direction can be easily performed. 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 detecting portion can be moved in the x-axis direction in accordance with the size of the irradiated body 1352605, the position in the desired portion can be confirmed. [Embodiment] Hereinafter, a preferred first embodiment of a strand irradiation apparatus according to the present invention will be described with reference to Figs. 1 to 5 . In the drawings, the same or corresponding elements are denoted by the same reference numerals, and the description thereof will not be repeated. The embodiment is described with respect to the case where the charged particle beam irradiation device is used as a proton line. As shown in Fig. 1 to Fig. 3, a device for irradiating a tumor (irradiation target) p and a sub-line (charged particle beam) in the proton-line treatment device 1 (in the irradiated body) 5 1 . The proton beam therapy device 100 includes a proton beam irradiation unit (charge irradiation unit) 1' which is attached to the rotating holder 1 chamber, and is rotatable around the treatment table (mounting table) 105. Φ The proton beam irradiation unit 1 includes an irradiation 17 for controlling the irradiation direction A in the order of the proton lines, the beam passing through the beam, and the beam morphing body 5, as shown in FIG. Ridge filter precision degrader 9, block type collimator 1 1, rapid injection 1 3, multi-right instrument 15, the drive of each part of the device.
將當作質子線產生部之功能的迴旋加速器3所 質子線’通過輸送裝置送入該質子線照射部1。然 由使被送入的細質子線，例如通過厚度數mm的鉛 的散射體（射束擴大部）5的方式，在照射方向A 的照射 荷電粒 説明中 明。本 治療裝 係對患 照射質 電粒子 〇3 (照 控制部 質子線 部7、 葉式準 產生的 後，藉 所構成 的正交 1352605 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「SOBPj )。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***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51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9a、9b所構成，利用，藉由由照射控制部17之控 制來調節上述擋塊9a、9b之重疊方式，可連續地變化質 子線通過部分的厚度。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- 1352605 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11。後述之多葉式準直儀15以外，此處進 行擋塊式準直儀11所進行之整形，係爲了不在患者附近 產生擋塊式準直儀Π造成的2次放射線。 通過該擋塊式準直儀11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）13,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13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13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15a、15b， 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 1 5c之位置及形狀變化。 通過多葉式準直儀15之質子線射束，被擷取出對應 上述開口 15c形狀之輪廓，因此多葉式準直儀15係以使 開口 1 5 c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- 1352605 照射在患者51。然後，藉由一面使多葉式準直儀 口 15c之平面位置及平面形狀變化，使照射域的 朝水平方向（照射方向A之正交方向）移動，一 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 視照射在照射域的照射線量之手段。線量監視器 在精密降能器9和擋塊式準直儀1 1之間，偵知 子線之線量。線量監視器23係將偵知之線量傳 控制部1 7當作監視器訊號s 1，照射控制部1 7可 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100設有用於取得患者 射線透視影像之X射線攝影裝置（X射線透視影 段）。該X射線攝影裝置具備X射線產生器、 患者5 1的X射線之X射線檢測器。該等X射線 X射線檢測器係固定在旋轉支架1 0 3，可在患者f 轉。本實施形態中，具備二個X射線產生器，該 線產生裝置係配置在相差90度之位置。且，在 X射線產生器之位置，配置X射線檢測器。X射 置係根據由X射線檢測器所檢測到的資料，作员 的X射線透視影像，而可檢測骨、金屬標記以 5 1之位置。 此處，質子線治療裝置100具備PET裝價 PET裝置31具有一對PET攝影機（檢測器）30 在旋轉支架103，且設定成可在治療台105周圍 15的開 位置順序 面反覆照 23，係監 23係設 通過的質 送到照射 根據監視 51的X 像取得手 檢測透射 產生器及 ίΐ周圍旋 :等X射 相對向於 線攝影裝 Ε患者5 1 測定患者 【3 1，該 ，係安裝 旋轉。即 -11 - 1352605 ，PET攝影機30和安裝在旋轉支架103之質 ，係設定成可一體地在X軸周圍旋轉。PET PET攝影機30之外，具備不圖示之影像處理 、顯示部等。影像處理部係根據由PET攝影H 之影像資訊，進行影像處理，產生PET影像。 錄被產生之PET影像等。被產生之PET影像 部而顯示。 該PET攝影機30係配置在治療台1〇5上ί 側，用於檢測消滅r射線。具體而言，對患者 中在腫瘤p之放射性藥劑（例如，11 c蛋氨酸 注入），PET攝影機30係檢測自腫瘤P (放射 達位置）產生的消滅7射線。PET裝置3 1係 射目標位置檢測手段之功能，該照射目標位置 根據PET攝影機30檢測消滅7射線的結果， 之位置。 且，PET攝影機30可檢測來自正電子放 r射線，該正電子放出核係因照射在患者51 入射質子核和腫瘤P内之原子核兩者之核反應 者’ PET裝置31係發揮當作質子線（荷電粒 位置檢測手段之功能，該質子線（荷電粒子線 檢測手段係根據PET攝影機30檢測消滅r射 檢測被照射的質子線實際在患者51體内之到 ’ PET裝置31係利用治療時使用的質子線之 和患者51體内中之原子核兩者的相互核反應 “線照射部1 :置31除了 部、記錄部 i 30所取得 記錄部係記 係藉由顯示 5患者5 1兩 5 1進行集 )之投藥（ 性藥劑之到 發揮當作照 檢測手段係 檢測腫瘤P 出核之消滅 的質子線之 所產生。再 子線）到達 )到達位置 線的結果， 達位置。即 入射質子核 ，從體内中 -12- 1352605, 所產生的正電子放出核種計測消滅T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33、沿著該支撐構件33朝X軸方向移動之X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35、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33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103之框l〇3a ( 參照第2圖）。支撐構件33係配置在旋轉支架1〇3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34，形成有用於導引X軸方向移動構件34 的移動方向之滑動導件38，X軸方向移動構件34係經由 滑動導件38被支撐成可在X軸方向移動。然後，χ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Υ軸方向延伸構件35及Υ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- 1352605 方向之滑動導件39，Y軸方向移動構件36係經由滑動導 件39被支撐成可在Υ軸方向移動。然後，γ軸方向移動 構件36係藉由固定在Υ軸方向延伸構件35之電動機40 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γ軸所正 交之Ζ軸方向（第5圖中的上下方向）延伸。輸出軸41 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γ軸方向延 伸構件35旋轉。驅動軸43的一對軸承44間設有齒輪45 。且，在驅動軸43之與耦合件42相反側的端部，設置有 制動器46及電位計47。 且，在Υ軸方向移動構件36，朝Υ軸方向形成有咬 合齒輪45之齒條48。然後，以旋轉驅動電動機40的方式 ，藉由齒輪45及齒條48傳達驅動力，使Υ軸方向移動構 件36朝Υ軸方向往返移動。藉此，可使PET攝影機30 對患者51接近。以將PET攝影機30配置成接近患者的方 式，提高消滅7射線之檢測精確度。 該PET攝影機30可藉由旋轉支架103的背面面板 1 〇 3 b而收納在背面側，計測時，藉由汽缸3 7驅動，且配 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之位置 調整的治療台位置控制部（載置台控制部）。然後，該治 療台位置控制部係根據由PET裝置31所取得之PET影像 、由X射線攝影裝置所取得之X射線透視影像，控制治 -14- 1352605 療台105之位置’且調整治療台105之位置，將質子線照 射在治療台1 〇 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5 1的腫瘤 P立體形狀所作成之腫瘤圖（目標物圖）19的資訊，一面 特別是控制脊形濾鏡部7、精密降能器9、及多葉式準直 * 儀15的動作。且，在此處將預先準備的快速注射13設置 . 在預定位置，使照射域最遠部的形狀對應腫瘤最大深度部 • 分複雜的形狀而被整形。 再者，照射控制部1 7係配合由PET裝置所檢測到的 質子線到達位置，進行質子線射束調整。即，照射控制部 17係控制脊形濾鏡部7、精密降能器9、及多葉式準直儀 15的動作，調整質子線射束，使患者51體内的質子線實 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治療裝置 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100時，PET攝影機30係處 於收納在背面面板1 03b背面側之狀態。此處舉一例説明 關於對腦腫瘤患者之質子線治療。首先，使患者51躺在 旋轉支架103内的治療台105上。患者51的長方向係配 . 置成沿X軸方向。接著，等候對患者5 1進行1 1C蛋氨酸 投藥（S1)、對腦腫瘤聚集蛋氨酸（S2)。接著，藉 由PET攝影機30測定聚集在腦腫瘤之UC蛋氨酸所放出 的消滅r射線（第1檢測步驟、S3)。此時，驅動汽缸 37 ’使PET攝影機30朝X軸方向移動而配置在患者51 -15- 1352605 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30彼此的間隔。進行3維影像測定時 ’使旋轉支架1 03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’藉由X射線攝影裝置進行透視攝影，作成患者51的 . X射線影像（X射線透視影像取得步驟），確認骨及金屬 • 標記位置。此外，亦可改變PET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 〇3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（S 6 )。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5 1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103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r射線之檢測。且，亦可使PET攝影機3 0旋轉，進 行測定。接著，根據PET攝影機3 0測定的結果，作成 -16- 1352605 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、S10)。 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、S11) »射束調整終 ，照射質子線（S12)。此外，亦可再度實施S8〜S11 根據這種質子線治療裝置100，可將PET攝影| 設在旋轉支架103，藉由該PET攝影機30，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r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30 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30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7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103的背面面板103b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ί 認實 内之 置偏 位置 了後 〇 I 30 射之 所產 之質 ) — 固定 ，使 隨即 之移 測定 且， 此可 向中 收納 PET i 30 -17- 1352605 之檢測範圍。且，藉由PET攝影機30適當移 使PET攝影機30不會妨礙質子線照射部1之 ，將患者51搬入、搬出旋轉支架103内時， 30不會造成妨礙。且，亦可配合被照射體的 PET攝影機30，因此容易確認所要部位之照射 且，PET攝影機30可朝夾住患者51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1 ，可提高消滅7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 I 台I 05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5 I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，説明本 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60a 處。 .動之方式， ，旋轉。再者 PET攝影機 大小而移動 位置。 向（Y軸方 的距離，因 | 51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- 1352605 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Y軸方 移動構件36内側的端部36a。該攝影機固定部62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之檢測面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r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100相同的效果，此外因爲PET攝影機60可在Y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 是 是 -19- 1352605 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， PE丁攝影機朝X軸方向之移動、朝Y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。 線 子 質 之 相 所 態 形 施 實 第 之 明 發 本 ] 示 明表 說係 單圖 簡 1 式第 圖 -20- 1352605 '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ό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 103 :旋轉支架（照射室） 105: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 -The proton line ' of the cyclotron 3 functioning as a proton generating unit is sent to the proton beam irradiating unit 1 by a transport device. However, the fine particle to be fed is, for example, a scatterer (beam enlargement portion) 5 having a thickness of several mm, and is described in the irradiation charge particle in the irradiation direction A. In the treatment device, the irradiated electrophoretic particle 〇3 (according to the proton line portion 7 of the control portion and the leaf pattern quasi-presence, the beam is expanded and expanded to a beam having a large width in the direction of the orthogonal 1352605. The proton beam beam of the body 5 corresponds to the thickness of the tumor P in the body of the patient 51 (the length of the irradiation direction A), and is incident on the ridge filter portion (peak 値 adjustment filter portion) 7, which is a ridge filter The faucet is for maintaining the energy depth distributed on the proton line. The ridge filter portion 7 has a plurality of filters 7a formed by arranging the metal rods in a stepwise manner to form a curtain, and the plurality of filters 7a forms an enlarged Bragg peak (hereinafter referred to as "SOBPj") having different proton lines from each other by different shapes of the metal rods. Then, the ridge filter portion 7 is driven by the control of the irradiation control unit 17, and has A filter that is appropriately selected from the plurality of filters 7a is inserted into a mechanism of a proton beam passing position. With this configuration, the ridge filter portion 7 can selectively change the filter 7a through which the proton beam passes. Adjust the width of the SOBP peak of the proton line. The proton line of the ridge filter portion 7 adjusts the beam energy in accordance with the depth of the tumor P in the patient's body 51, and is incident on the precision energy reducer for adjusting the maximum depth of arrival (beam energy adjustment) The precision degrader 9 is composed of, for example, two polypropylene stoppers 9a and 9b forming a wedge shape, and the stopper 9a is adjusted by the control of the irradiation control unit 17, The overlapping manner of 9b can continuously change the thickness of the proton passing portion. The proton line loses energy due to the thickness of the material passing through, and changes the depth of arrival in the body of the patient 51, so the precision degrader can be adjusted by 9 The position of the SOBP of the proton line is matched to the position of the depth direction of the tumor P (irradiation direction A) in the patient 51. The proton beam beam passing through the precision degrader 9 is incident on the proton used for the -9- 1352605 The planar shape of the line (the shape seen from the irradiation direction A) is a roughly shaped block type collimator 11. In addition to the multi-leaf collimator 15 described later, the shaping by the stopper type collimator 11 is performed here. In order not to be produced near the patient The secondary radiation caused by the block collimator 。. The proton line of the block type collimator 11 is input to, for example, a resin-made non-shaping filter, that is, a rapid injection (compensation filter) 13 for the tumor P. The cross-sectional shape and the tissue inhomogeneity of the maximum depth are corrected. The shape of the rapid injection 13 is calculated based on the tumor contour 'and the electron density of the surrounding tissue obtained from the data of X-ray CT, for example. The method of rapid injection 13 is such that the three-dimensional shape of the farthest part of the proton beam (the maximum reaching depth portion) is shaped in accordance with the shape of the maximum depth portion of the tumor P, so that the linear concentration of the tumor P can be further improved. The rapid injection of a proton beam beam of 13 is incident on a multi-leaf collimator (shape variable collimator) 15. The multi-leaf collimator 15 is composed of two blind portions 15a and 15b 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 allows the proton beam to pass through the opening 15c such that the plurality of comb teeth are advanced and retracted in the longitudinal direction by the shielding portion 15a' 15b. The position and shape change. By the proton beam of the multi-leaf collimator 15, the contour corresponding to the shape of the opening 15c is extracted, so that the multi-leaf collimator 15 can obtain the incident proton in such a manner that the shape of the opening 15c is changed. The desired planar position and planar shape of the line beam. The proton beam beam having the desired planar shape obtained at the desired planar position is irradiated to the patient 51 by -10- 1352605 as a therapeutic proton. Then, by changing the plane position and the planar shape of the multi-leaf collimator port 15c, the irradiation direction is moved in the horizontal direction (the orthogonal direction of the irradiation direction A), and the entire tumor P is irradiated in a single shot. Proton beam. Further, the one-probe ray irradiation unit 1 is provided with means for the line amount monitor to illuminate the amount of irradiation light in the irradiation region. Line Quantity Monitor Detects the amount of line between the sub-line between the precision degrader 9 and the block collimator 11. The line amount monitor 23 uses the detected line amount transmission control unit 17 as the monitor signal s 1, and the illumination control unit 17 detects the amount of illumination applied to the illumination field by the illumination signal s 1 . Further, the proton therapy device 100 is provided with an X-ray imaging device (X-ray fluoroscopic image) for acquiring a patient's fluoroscopic image. This X-ray imaging apparatus includes an X-ray generator and an X-ray X-ray detector of the patient 51. The X-ray X-ray detectors are fixed to the rotating support 103 and can be rotated in the patient f. In the present embodiment, two X-ray generators are provided, and the line generating devices are disposed at positions that differ by 90 degrees. Further, an X-ray detector is disposed at the position of the X-ray generator. The X-ray is based on the X-ray fluoroscopic image of the person detected by the X-ray detector, and the bone and metal marks can be detected at positions 51. Here, the proton therapy device 100 is provided with a PET-packed PET device 31 having a pair of PET cameras (detectors) 30 in the rotating holder 103, and is set so as to be sequentially reversed 23 in the open position of the periphery 15 of the treatment table 105. The quality of the 23 series is passed to the illumination. According to the X image of the monitor 51, the hand detection transmission generator and the surrounding rotation are obtained. The X-ray is opposite to the line imaging device. 5 1 The patient is measured. [3, this is installed. Rotate. That is, -11 - 1352605, the PET camera 30 and the mass mounted on the rotating bracket 103 are set to be rotatable integrally around the X-axis. In addition to the PET PET camera 30, there are image processing, display units, and the like which are not shown. The image processing unit performs image processing based on the image information of the PET image H to generate a PET image. Record the resulting PET images and so on. Displayed in the generated PET image section. The PET camera 30 is disposed on the side of the treatment table 1〇5 for detecting the elimination of r rays. Specifically, for a radiopharmaceutical (e.g., 11 c methionine injection) in tumor p in a patient, PET camera 30 detects the eradicated 7-ray generated from tumor P (radiation reaching position). The PET device 3 1 functions as a target position detecting means for detecting the position at which the 7-ray is eliminated based on the PET camera 30. Further, the PET camera 30 can detect a positron-releasing r-ray which is a nuclear reactor (the PET device 31 that functions as a proton line by irradiating both the patient 51 into the proton nucleus and the nuclei in the tumor P). The function of the charged particle position detecting means, the charged particle line detecting means is based on the detection by the PET camera 30 that the proton beam to be irradiated is detected in the body of the patient 51, and the PET device 31 is used for treatment. Mutual nuclear reaction between the protons and the nuclei in the body of the patient 51. "Line irradiation unit 1: Set 31 except for the portion, and the recording unit i 30 obtains the recording unit line by displaying 5 patients 5 1 2 5 1 The drug is administered as a means of detecting the proton line of the extinction of the tumor P. The sub-line arrives at the position line and reaches the position. That is, the incident proton nucleus, from In vivo -12- 1352605, the generated positron emission nucleus measurement eliminates T-rays, and determines the intensity distribution of each produced nucleus', thereby detecting the actual proton line in the patient 51 to Position shown in FIG. 30 the PET camera system of Figure 4, can be moved toward the rotational center axis of rotation X 1〇3 holder (hereinafter referred to "X axis") direction of movement, and is movable toward Y-axis direction orthogonal to the X-axis. The PET camera support portion 32 each supporting the pair of PET cameras 30 has a support member 33 extending in the X-axis direction, an X-axis direction moving member 34 moving in the X-axis direction along the support member 33, and being disposed in the X-axis direction. The Y-axis direction extending member 35 in which the front end portion 34a of the moving member 34 extends in the Y-axis direction and the Y-axis direction moving member 36 that moves 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 which projects outward in the Y-axis direction, and the projecting portion 33a is fixed to the frame l3a of the swivel bracket 103 (refer to Fig. 2). The support member 33 is disposed on the back side (the right side of the drawing) of the back panel 1 0 3 b of the rotary holder 1〇3. The support member 33 and the X-axis direction moving member 34 are formed with a slide guide 38 for guiding the moving direction of the X-axis direction moving member 34, and the X-axis direction moving member 34 is supported via the slide guide 38. Move in the X-axis direction. Then, the yaw-axis 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 39 for guiding the movement of the γ-axis direction moving member 36 in the direction of -1325605 is provided, and the Y-axis direction moving member is provided. The 36 is supported via the slide guide 39 so as to be movable in the z-axis direction. Then, the γ-axis direction moving member 36 is driven by the motor 40 fixed to the y-axis direction extending member 35, and is reciprocally movable in the y-axis direction. The motor 40 is disposed such that its output shaft 41 extends in the z-axis direction (vertical direction in Fig. 5) orthogonal to the X-axis and the γ-axis. The output shaft 41 is coupled to the drive shaft 43 that extends in the x-axis direction via the coupling member 42. The drive shaft 43 is supported by a pair of bearings 44' so as to be rotatable in the γ-axis direction extending member 35. A gear 45 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, the rack member 48 is moved in the z-axis direction to form a rack 48 of the meshing gear 45 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 30 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 the 7-ray elimination is improved. The PET camera 30 can be housed on the back side by the back panel 1 〇 3 b of the swivel bracket 103, and is driven by the cylinder 37 during measurement, and is disposed 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 position of the treatment-14-1352605 treatment table 105 based on the PET image acquired by the PET device 31 and the X-ray fluoroscopic image acquired by the X-ray imaging device, and adjusts the treatment table 105. At the position, the proton beam is irradiated to the tumor P of the patient 51 on the treatment table 1 〇5. The irradiation control unit 17 controls the ridge filter portion 7, the precision degrader 9, and the like, with reference to the information of the tumor map (target map) 19 which is stored in the three-dimensional shape of the tumor P according to the patient 51. And the operation of the multi-leaf collimation device 15. Further, a quick injection 13 prepared in advance is set here. At a predetermined position, the shape of the farthest portion of the irradiation region is shaped corresponding to the maximum depth portion of the tumor. Further, the irradiation control unit 17 performs the proton beam beam adjustment in accordance with the proton line arrival position detected by the PET apparatus. That is, the irradiation control unit 17 controls the operations of the ridge filter unit 7, the precision degrader 9, and the multi-leaf collimator 15, and adjusts the proton beam beam so that the proton line in the patient 51 actually reaches the position and The location of tumor P is consistent. Next, a proton beam irradiation method (charged particle beam irradiation method) using the proton therapy device 1 thus configured will be described. ® When the proton therapy device 100 is not used, the PET camera 30 is placed on the back side of the back panel 103b. Here is an example of proton therapy for patients with brain tumors. First, the patient 51 is placed on the treatment table 105 in the rotating stent 103. The long direction of the patient 51 is tied. It is placed along the X-axis direction. Next, it is waited for the patient 1 1 to carry out 1 1 C methionine administration (S1), and for brain tumors to aggregate methionine (S2). Next, the extinction r-ray emitted by UC methionine accumulated in the brain tumor is measured by the PET camera 30 (first detection step, S3). At this time, the driving cylinder 37' moves the PET camera 30 in the X-axis direction and is disposed on both sides of the patient 51 -15 - 1352605. The driving 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, 'Rotate the rotating holder 203 to measure the r-ray. Then, based on the result of measurement by the PET camera 30, a PET image is produced to detect the position of the brain tumor (the irradiation target position detecting step, S4). The X-ray image (X-ray fluoroscopic image acquisition step) of the patient 51 is created by fluoroscopy by an X-ray imaging apparatus to confirm the position of the bone and the metal mark. In addition, it is also possible to change the order of PET photography and X-ray photography, or to perform multiple photography alternately. Further, the rotation bracket 1 〇3 is rotated in accordance with the necessity to change the positions of the X-ray generator and the X-ray detector. Then, based on the PET image and the X-ray image, the irradiation plan is established (S 6 ). 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 position adjustment of the treatment table 105 (the stage setting adjustment step, S7) is performed based on the determined irradiation plan, and the patient 51 is placed at an appropriate position. Then, 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 PET camera 30 " is used to measure the extrinsic r-ray from the positron emission nucleus generated by the nuclear reaction between the irradiated proton line and the nuclei in the patient 5 1 (second detection step, S9). At this time, the PET cameras 30 are moved in the Y-axis direction in such a manner that they approach each other, and the PET camera 30 is brought close to the patient 51, and the detection of the r-rays is eliminated. Further, the PET camera 30 can be rotated to perform measurement. Then, based on the result of the PET camera 30 measurement, the -16 - 1352605 PET image is prepared to detect the proton line arrival position in the patient 51, and the irradiation field is confirmed (the charged particle beam arrival position detecting step, S10). 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 displacement, the beam adjustment is performed so that the proton beam is irradiated within the allowable range of the irradiation target (shooting Beam adjustment step, S11) » Beam adjustment end, illuminate the proton line (S12). Further, S8 to S11 may be re-executed. According to the proton therapy device 100, PET imaging|photographs can be provided on the rotating holder 103, and the PET proton 30 can measure the incident proton nucleus of the illuminated proton and the nucleus in the tumor. The positron-emitting nucleus of the two reacts to eliminate the r-ray, so that the actual arrival position of the irradiated 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 30 is rotated by the holder 103, the rotary PET camera 30, which can be engaged with the rotary holder 103, rotates around the patient 51 to irradiate the proton line, and then the measurement of the extinction of the r-ray is performed. Further, the degree of freedom of motion 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. Since the PET camera 30 and the proton beam irradiation unit 1 rotate in synchronization, the detection of the 7-rays is performed while maintaining the positional relationship between the rotation of the PET camera 30 and the proton beam irradiation unit 1, and the PET camera 30 can be oriented in the X-axis direction. It is moved and can be on the back side of the back panel 103b of the swivel bracket 103. In such a manner that the camera 30 is moved in the X-axis direction, the position of the PET camera can be enlarged, and the position of the camera 30 can be increased, and the result of the measurement can be adjusted. The detection range of PET i 30 -17- 1352605 is accommodated. 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 used, 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 gripped, since the PET camera can be arbitrarily changed by the PET camera. 30 is close to the 1 in the Y-axis direction, which improves the detection accuracy of eliminating 7 rays. 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-line irradiation method of the present invention, in the irradiation room, the patient can be swollen using the PET camera 30 in a state of 5 I I 05, and the tumor position and the actually irradiated proton line can be corrected to be offset. , position patient 5 I 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 the present 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 a position where the PET camera 60 of the second embodiment rotates further and the detection surface 60a of the PET camera 60. The way of moving, rotating. Furthermore, the PET camera moves in size. The distance to the (Y-axis) is due to the fact that the high-precision head fixation device and the position at the position where the treatment tumor is located at the position of the treatment can be highly fixed and reduced: the second embodiment of the invention 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 Y-axis side, and the phase of the Y-axis is different from the -18-3522605. An end portion 36a on the inner side of the member 36. The camera fixing portion 62 mounts a motor 63 for rotationally driving the PET camera 60. The output shaft 64 of the motor is disposed in the Y-axis direction. Then, the transport shaft 64 of the motor 63 is connected to the PET camera. 60. It is rotatable around the Y-axis. The detecting surface 60a of the PET camera 60 is curved in an arc shape, and one detecting surface 60a is disposed to face each other. When the PET camera 60 is moved in the X-axis direction, it is configured. The long direction is along the X-axis (state shown in Fig. 7). When measuring r-rays, the PET camera is arranged such that the central axis of the arc is parallel to the X-axis direction. Parallel position makes PET camera 60 The rotation is performed and measured from various angles. In this configuration, the same effect as the proton therapy unit 100 of the first embodiment can be obtained, and since the PET camera 60 can be rotated around the Y-axis, the movement of the PET camera 60 can be further improved. The degree of freedom 'is possible to improve the measurement accuracy by measuring the irradiation position in various directions. The present invention is not limited to the first embodiment and the second embodiment (hereinafter referred to as "the above embodiment"). The camera is set to be rotatable around the X axis 'but it may not be rotated around the axis, or it may be rotated in other directions. The PET camera is configured to move in a direction close to each other' but the PET camera may not The movement in the direction of approaching each other. And 'Although the direction of the camera is 63 out of the direction 60 is in the shape of the circumference» X is -19- 1352605 Use the cylinder, motor to move the PET camera, but also use the hydraulic cylinder Other driving devices such as linear motors move the PET camera. Moreover, the PE camera moves in the X-axis direction toward Y. The movement of the direction may not be linear, or may be a curved or arcuate movement. Further, in the above embodiment, the PET camera is attached to the rotating holder, and is rotatable around the X-axis integrally with the proton beam irradiation unit, but PET The 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 may be separately provided, and the PET camera may be rotated by following the rotation of the rotating bracket and the proton beam irradiation unit. 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. The phase of the phase of the line is applied to the state of the body. The description of the table is shown in the figure. Figure 1 - 1352605 'The perspective view of the treatment device. 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. The figure 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 7 VIII-VIII. [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 103 : Rotating stand (irradiation chamber) 105: Treatment table (mounting table) P : Tumor (irradiation target) X : X-axis direction Y : Y-axis direction - 21 -