M336031 一 七、指定代表圖·· (一） 本案指定代表圖為：第（一）圖。 (二) 本代表圖之元件符號簡單說明： 10電源器 11光源器 12輸出光 13光斑大小控制器（簡稱光斑器） 14聚透鏡 20掃描器 21、22 45度高反鏡 40 45度高反鏡 41眼球表面治療區 八、新型說明： 【新型所屬之技術領域】 φ 本實用新型涉及一種固體雷射眼科治療儀，用於治療近視、遠視、 ，光及老視等病症，治療這些病症的方法總稱為角膜原位成形磨鑲 術(LASIK) ’本實用新型尤其是提供一種用於這種手術的高效率飛 點掃描雷射視力治療儀。 【先前技術】 目，市％上用於LASIK的雷射視力治療儀均使用有毒氣體氟化氬 CArF)的準分子雷射(ExCimer Laser)，此設備在維修時及使用、 製造的安全性、成本各方面均有劣勢。非準分子固體雷射系統用 於LASIK，由於技術及臨床上未能有所突破，至今尚缺。特別是在 龜 其波長在到220奈米的深紫外及波長在2· 7到3 〇微米的中 • 紅外兩個波長區，沒有相應的雷射視力治療設備。再者現有準分 子雷射光斑大小不可調，切除效率及準確性兩者都受限制。 【新型内容】 發明目的及概述： 含實用新型的目的在於突破現有技術的缺陷，提供一種克服低能 量，低重複頻率障礙，可調光斑大小以達到切除效率及準確性的實 ，應用要求，可用於LASIK的雷射視力治療的南效率飛點掃描雷射 視力治療儀。 ” 〜 發明詳細說明： 本實用新型的目的是這樣實現的： 本實用新型提供的高效率飛點掃描雷射視力治療儀，包括一光源器 4 M336031 卞一知描器，所述光源器與電源相連接 光源器後面的光路上設有所述掃描考，在先束，在所述 有起到聚光作_-輯鏡之間還設 ，設有—可改縣束光斑大小的光斑調ϋ置。❽之間的光路上 本^效率飛點掃描雷射視力治療儀中所述的 -用於控制在眼球*面位置光斑的大小1 源器和聚透鏡之間的光路上。 九斑器其汉置在所述光 該光斑器可以是現有技術中的改變光斑大小哭 =光斑調_置也可岐可麵述統° 的光斑大小改變賴述聚魏。 ㈣W歧I透過匕 光源器可為氟化氬(ArF)的準分子光源 (=) ’ 統⑽或氬 d(Y：^ S3 〇=%，=、雷射二極’雷射器，紅外波長2.7 』長為冗到ί di也可以使用閃燈（f lashlamp)泵或雷射二極管（diode ，光源器也可以是使用拉曼管（Raman Cell)產生的拉曼頻 之參鈥（Nd)氬鉻（YAG)，氬氟（YLF)或氬氟氧 2yp4)的固體雷射器，輸出波長為2 7到3 〇微米（micr〇n)，該拉 又管長為0·2到1·5米。管内高壓氣體可以是氫氣(H2)、氘(D2)或甲 燒(mathane)，高壓範圍400到9〇〇碎/平方英寸(pSi)。 所述光源器本身可以是包括2個獨立光源體構成，該兩個獨立光源 體的出光相對時間不同時，即相對延遲時間（T)0 005到〇· 1秒之 間，並使用掃描速度在1/Τ到3/Τ (毫米/秒)之間，並使用掃描速 度在每秒^100毫米到50毫米之間；以達到”有效，，重複頻率相加效 果’而提高切除效率，這是單一光線做不到的。還包括一個合光器， 其内包含一對45度反射鏡，其中一個反射鏡設在一個獨立光源器的 輸出光路上，使得該光線穿透該反射鏡，另一反射鏡設在另一個獨 立光源器的輸出光路上，使得該光線反射，並經前一個反射鏡反射 與透射光線組合為同軸光路的光線到達所述掃描器。 所述兩個獨立光源器發出的兩輸出光的線性偏振方向 (linear-polarization)相互垂直。 所述光源器和合光器之間可以設有光斑器，在每束雷射光束的光路 上各設置一個光斑器。 5 'M336031 透鏡H纟ι合絲㈣社設置一個 J實現克鏡3的掃描器’使之分別在x及γ軸向轉 ΐ，低重複頻率障礙，以達到實際應用的要 Φ 器可ϊϋίϊϊίίίί治療的目的。通過進一步設置的光斑 i性。v確保同效率角膜表面切除，並能同時保持切除的準 以上特點可在下列具體實施例中進一步明確。 【實施方式】 最佳實施例： 實施例1 ·· 本m飛點掃描雷射視力治療儀中，其光源器 ii，-气制並輸出到達眼球表面治療區41的光斑大 ϋ此置。該輸出先12通過聚透鏡再經由一掃描器20及一 45度高反 鏡40，將雷射能量傳輸到眼球表面治療區41。 高反鏡21及22，與轉動馬達連接，分別 秦’其知插*式由電腦軟件控制。該光斑器13可以是 調裝置，例如相機鏡頭裝置以及類似裝 置、’、、巫由機械或電控7〇件控制其圓形隙孔的開口度。其可調開口大 為1· 0到7· 0毫米直徑，以達到聚焦後輸出光丨2在眼球治療區41， 光斑大小可調範圍為0· 3到3· 0毫米直徑，本實用新型的特點是可以 確巧高巧率^膜表面切除，並能同時保持切除準確性，此功能可經 由光斑器13提供大、中、小光斑，提供光斑的直徑範圍分別為1 到3· 0毫米’ 1· 3到1· 7毫米，〇· 5到1· 2毫米，分別使用在大、中、 小切^區，直控範圍分別為3· 〇到7· 〇毫米，2· 1到2· 9毫米，〇· 3到 2· 0毫米實現。也可以是使用大小兩種光斑，其直徑範圍分別為l 5 M336031 到3·0毫米，0·5到1·4毫米。 該掃描方式可經由林氏公式，參考文獻(Lin，JT. Customized bifocal lasik profiles for presbyopic eyes ， Customized LASIK ’ In: Garg A，Lin JT，ed· New Delhi: Jaypee Brothers Medical Publishing· .2007)中所定義的角膜切除函數(ablation profile)達到近遠視、散光及雙焦距(bif0Cai)等不同視力矯正。 大光斑切除效率高，但失去其準確性，特別是在角膜中央區〇到2· 〇 毫米，因其弧形函數（profile)，小光斑有較高的準確性，但效率 低。本實用新型综合上述兩者的優點，取其優勢以達到高效率及高 準確性。M336031 VII. Designation of Representative Representatives (1) The representative representative of the case is: (1). (2) The symbol of the representative figure is briefly described: 10 power supply 11 light source 12 output light 13 spot size controller (abbreviated as spot) 14 poly lens 20 scanner 21, 22 45 degree high mirror 40 45 degree high anti Mirror 41 eye surface treatment area VIII, new description: [New technical field] φ The utility model relates to a solid laser ophthalmic therapeutic apparatus for treating diseases such as myopia, hyperopia, light and presbyopia, and treating these diseases The method is generally referred to as corneal in situ atherectomy (LASIK). The present invention provides, inter alia, a high efficiency flying spot scanning laser vision treatment apparatus for such surgery. [Prior Art] The laser vision treatment instrument for LASIK uses the ExCimer Laser, a toxic gas argon fluoride (ARRF), which is used for maintenance and safety during use and manufacture. Costs have disadvantages in all aspects. The non-excimer solid-state laser system used in LASIK has not been broken due to technical and clinical breakthroughs. Especially in the dark ultraviolet of the turtle with a wavelength of up to 220 nm and the two wavelengths of the wavelength of 2.7 to 3 μm, there is no corresponding laser vision treatment equipment. Furthermore, the size of the existing quasi-molecular laser spot is not adjustable, and both the removal efficiency and the accuracy are limited. [New content] The purpose and summary of the invention: The purpose of the utility model is to break through the defects of the prior art and provide a real and application requirement for overcoming low energy, low repetition frequency obstacle, adjustable spot size to achieve cutting efficiency and accuracy. The Southern Efficiency Flying Point Scanning Laser Vision Apparatus for Laser Vision Treatment at LASIK. ～ Detailed Description of the Invention: The object of the present invention is achieved as follows: The high-efficiency flying spot scanning laser vision treatment instrument provided by the utility model comprises a light source 4 M336031, and the light source is connected with a power source. The scanning path is arranged on the optical path behind the light source, and is provided in the first beam, and is arranged between the concentrating mirror and the mirror, and is provided with a spot concentrating device capable of changing the size of the beam spot of the county. The optical path between the ❽ ^ ^ 效率 效率 扫描 扫描 扫描 扫描 扫描 扫描 扫描 扫描 扫描 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率 效率In the light, the spotter can be changed in the spot size in the prior art, and the spot size change can be described as a change in the spot size. (4) W-I can be argon fluoride through the xenon light source. (ArF) excimer light source (=) 'system (10) or argon d (Y: ^ S3 〇 =%, =, laser two-pole 'laser, infrared wavelength 2.7 』 long to be redundant to ί di can also use flash Lamp (f lashlamp) pump or laser diode (diode, light source can also be used to pull A Raman cell-generated Raman-frequency (Nd) argon-chromium (YAG), argon-fluorine (YLF) or argon-oxygenated 2 yp4 solid-state laser with an output wavelength of 27 to 3 μm (micr) 〇n), the length of the tube is from 0. 2 to 1.5 meters. The high pressure gas in the tube can be hydrogen (H2), helium (D2) or mathane, and the high pressure range is 400 to 9 min/square inch. (pSi) The light source itself may be composed of two independent light source bodies, and the light-emitting time of the two independent light source bodies is different, that is, the relative delay time (T) is between 0 005 and 〇·1 second, and Use scan speed between 1/Τ and 3/Τ (mm/s) and use scan speed between ^100 mm and 50 mm per second; to achieve "effective, repeat frequency addition effect" to improve resection Efficiency, which is not possible with a single ray. Also included is a light combiner that includes a pair of 45 degree mirrors, one of which is placed on the output light path of an independent light source such that the light penetrates the reflection a mirror, another mirror is disposed on the output light path of another independent light source, so that the light is reflected and passed through the previous one Between the mirror reflection and the transmitted light, the light of the coaxial optical path reaches the scanner. The linear polarization of the two output lights emitted by the two independent light sources is perpendicular to each other. The light source and the light combiner There may be a spotter, and a spotter is arranged on each of the beams of the laser beam. 5 'M336031 Lens H纟ι (4) Set a J to implement the scanner of the mirror 3 to make it in x and γ axial transition, low repetition frequency barrier, in order to achieve the purpose of practical application of Φ ϊϋ ϊϋ ϊϊ ϊϊ ϊϊ ί 。. By further setting the spot i property. v Ensure that the corneal surface is removed with the same efficiency, and that the characteristics of the resection can be maintained at the same time. The above features can be further clarified in the following specific examples. [Embodiment] Preferred Embodiment: Embodiment 1 In the present m-point scanning laser vision treatment apparatus, the light source ii, the gas source and the light output to the surface treatment area 41 of the eyeball are larger than this. The output 12 transmits the laser energy to the eye surface treatment zone 41 through the condenser lens and through a scanner 20 and a 45 degree mirror. The high-reflection mirrors 21 and 22 are connected to the rotating motor, and respectively, Qin's knowledge of the plug-in type is controlled by computer software. The spot 13 can be a modulating device, such as a camera lens device and the like, and the opening degree of its circular aperture is controlled by a mechanical or electronic control. The adjustable opening is substantially 1·0 to 7.5 mm in diameter to achieve the output after the focusing of the pupil 2 in the eye treatment area 41, and the spot size is adjustable from 0·3 to 3.0 mm diameter, the utility model The feature is that the high-definition film surface can be cut off and the cutting accuracy can be maintained at the same time. This function can provide large, medium and small spots through the spotter 13 and provide the spot diameters ranging from 1 to 3.0 mm. 1·3 to 1·7 mm, 〇·5 to 1·2 mm, respectively used in the large, medium and small cut areas, the direct control range is 3·〇 to 7·〇 mm, 2·1 to 2· 9 mm, 〇 · 3 to 2.0 mm achieved. It is also possible to use two types of spot sizes, ranging from l 5 M336031 to 3.0 mm, 0. 5 to 1.4 mm. This scanning method can be performed by Lin, JT. Customized bifocal lasik profiles for presbyopic eyes, Customized LASIK 'In: Garg A, Lin JT, ed· New Delhi: Jaypee Brothers Medical Publishing. 2007. The defined ablation profile achieves different vision corrections such as near-farsightedness, astigmatism, and bifocal (bif0Cai). The large spot removal efficiency is high, but its accuracy is lost, especially in the central region of the cornea, which is 2·〇 mm. Due to its curved profile, the small spot has high accuracy but low efficiency. The utility model combines the advantages of the above two, and takes advantages to achieve high efficiency and high accuracy.
該光源器11可為參歛(Nd)之氬鉻(YAG)，氬氟(YLF)或氬氟氧(YV04) 之固體雷射，經由非線性晶體轉變之紫外波長，〇· 2到〇. 27微米 (micron)或經由光諧振(optical parametric oscillation)轉變之 紅外波長2· 7到3·0微米。該光源器也可以是雷射二極管紅外波長 2.7到3.0微米，或參餌(£1〇之氬鉻(丫八6)或氬斯基(¥3〇〇)，輸出波 長為2· 7到3· 0微米（micron)。該光源器11也可以是使用拉曼管 (Raman Cell)產生的拉曼頻移(Raman-Shift)之參鈥(Nd)氬鉻 似0)，氬氟(¥1^)或氬氟氧(丫漏）的固體雷射器；輸出波長為2.7 到米(micron)，該拉曼管長為〇· 2到1· 5米。管内高壓氣體可 以是氫氣(H2)，氘(D2)或曱烧(mathane)，高壓範圍4〇〇到900碎/平 方英寸(psi)。 該光源器11可以使用閃燈(f lashlamp)泵或雷射二極管（di〇de laser)泵固體雷射。該輸出光12，脈沖寬度為〇· 〇i批可秒 (picoseconds)到500奈秒(nanoseconds)，重複頻率為5到 1〇 〇〇〇 嚇茲(Hz)，單脈沖能量為〇· 〇1到20毫焦（mj)。 ” ’ 實施例2 : 如第二圖所示，該聚透鏡14用於取代光斑器13，該聚透鏡14位 置可從距離A調整到距離B，聚透鏡焦距範圍（F)為3〇〇到15〇〇毫 米’該A及B距離為〇· 5F到1· 2F之間，所示在眼球表面位置光斑大小 45相對應由小變大，光斑直徑範圍〇· 3到3 〇毫米。 實施例3 : · /、 如第三圖所示，光源器11本身經由2個獨立光源體51及52構成，其 出光相對時間要求不同時，即相對延遲時間（τ)〇 〇〇5到〇丨秒之 間，並使用掃描速度在1/Τ到3/Τ (毫米/秒)之間·。以達到·"有效” 重複頻率相加效果，而提高切除效率，這是單一光線做不到的。該 7 M336031 光源體51及52之輸出光53、54，再經由一合光器60，其内包含一 對45度反射鏡61及62，組合為同軸光路到達掃描器20。達到該合光 器60之功能，要求輸出光53及54的線性偏振方向（Hnear polarization)相互垂直。該同轴光路的功能是可以簡化掃描器2〇 的軟件設計。 實施例4 ·· 如實施例1所示的該光斑器13，可置於實施例2中該組合線53或54 通路上，在每束雷射光束的光路上各設置一個光斑器13 ;或介於該 合光器60及聚透鏡14之間，在組合光束的光路上設置一個光斑器， 以控制其到達眼球表面位置41的光斑大小，其結構和原理如實施 例1中所述。The light source 11 can be a solid laser of argon-chromium (YAG), argon fluoride (YLF) or argon-oxygen (YV04), which is converted to a UV wavelength of a nonlinear crystal, 〇·2 to 〇. The infrared wavelength of 27 micron (micron) or optical parametric oscillation is 2. 7 to 3.0 micron. The light source can also be a laser diode with an infrared wavelength of 2.7 to 3.0 microns, or a bait (£1 argon chrome (丫8-6) or argon (¥3〇〇), with an output wavelength of 2.7 to 3 0 micron (micron). The light source 11 can also be a Raman-like (Raman-Shift) Raman-Shift-based (Nd) argon-chromium-like 0), argon fluoride (¥1) ^) or an argon-oxygen (drain) solid laser; the output wavelength is 2.7 to micron, and the Raman tube is 〇·2 to 1.5 m. The high pressure gas in the tube may be hydrogen (H2), helium (D2) or mathane, and the high pressure range is from 4 to 900 pieces per square inch (psi). The light source 11 can pump a solid laser using a flash lamp pump or a laser diode. The output light 12 has a pulse width of 〇· 〇i picoseconds to 500 nanoseconds, a repetition frequency of 5 to 1 〇〇〇〇 scary (Hz), and a single pulse energy of 〇·〇1 Up to 20 millijoules (mj). 'Example 2: As shown in the second figure, the condensing lens 14 is used to replace the spotter 13, the position of the condensing lens 14 can be adjusted from the distance A to the distance B, and the focal length (F) of the lenticular lens is 3 〇〇 to 15 〇〇 mm 'The distance between A and B is between 〇·5F and 1·2F, and the spot size 45 on the surface of the eyeball is correspondingly changed from small to large, and the spot diameter ranges from 到·3 to 3 〇 mm. 3: · /, As shown in the third figure, the light source 11 itself is constituted by two independent light source bodies 51 and 52, and the relative light emission time is different, that is, the relative delay time (τ) 〇〇〇 5 to leap seconds Between, and use the scanning speed between 1 / Τ to 3 / Τ (mm / s) · to achieve · &"; effective" repetition frequency addition effect, and improve the cutting efficiency, which is impossible for a single light . The output lights 53, 54 of the 7 M336031 light source bodies 51 and 52 are further passed through a combiner 60 which includes a pair of 45 degree mirrors 61 and 62 which are combined into a coaxial optical path to the scanner 20. Achieving the function of the combiner 60 requires that the linear polarization directions of the output lights 53 and 54 be perpendicular to each other. The function of the coaxial optical path is to simplify the software design of the scanner. Embodiment 4: The spotter 13 as shown in Embodiment 1 may be placed on the combined line 53 or 54 of the embodiment 2, and a spot 13 is disposed on each optical path of the laser beam; or Between the light combiner 60 and the condenser lens 14, a spot is disposed on the optical path of the combined beam to control the spot size of the eyeball surface position 41. The structure and principle are as described in Embodiment 1.
實施例5 如2四圖所示，所述光源器是包括2個獨立光源體構成，該兩個獨 立光源體為出光相對時間不同時的兩個光源體，即相對延遲時間τ 在〇· 005到0· 1秒之間，並使用掃描速度在1/τ到3/τ (毫米/秒)之間 的掃描器；在每個光源體的輸出光路上順序設有一個所述聚透鏡14 和一個所述掃描器20。 兩個獨立光源體輸出的該輸出光53及54分別由一對聚透鏡14聚焦 ^兩組掃描器20，該兩組掃描器20可由軟件分別獨立控制，將能^ ΐ輸Ϊ眼ί表面，以達到臨床要求之切除圖形。該組聚透鏡之焦距 可以疋相等或不等，分別控制其到達眼球表面位置相等或不等之光 斑大小。 實施例6 本實施例中包括前述實施例3中提_具有兩個 ί 源^發出兩束輸出光53、54，該兩侧立光源體 气時财同時的兩個光源體’即械延遲時間τ在0.005 相並使>用婦描速度在1/Τ到3/Τ (毫米/秒)之間的掃 ，在1^個彳f立光源體的輸出光路53、54上分別設置有二對反射 ί行而丄該兩對反射鏡的位置為：使得形成兩個幾乎 路的兩束光線’該靠近程度為使得該兩束光 二個播πί /後一個掃描器上，進而投射到其後面設置的同 謔當靠近的光路’再經由同-個掃讎 以上所述是本實用難的具體#闕及所雜術原理，不是對Embodiment 5 As shown in FIG. 4, the light source is composed of two independent light source bodies, and the two independent light source bodies are two light source bodies when the light exiting time is different, that is, the relative delay time τ is 〇·005 Between 0 and 1 second, and using a scanner with a scanning speed between 1/τ and 3/τ (mm/s); one of the polylenses 14 is sequentially disposed on the output light path of each of the light source bodies One of the scanners 20. The output lights 53 and 54 output by the two independent light source bodies are respectively focused by a pair of condenser lenses 14 by two sets of scanners 20. The two sets of scanners 20 can be independently controlled by software, and can be used to transmit the surface of the eye. To achieve the clinical requirements of the resection pattern. The focal lengths of the group of lenticular lenses can be equal or unequal, respectively controlling the spot size at which the positions on the surface of the eyeball are equal or unequal. Embodiment 6 In this embodiment, the foregoing embodiment 3 includes two sources of light, and two output lights 53, 54 are emitted. τ is at 0.005 phase and > sweeps between 1/Τ and 3/Τ (mm/sec) with a woman's drawing speed, and two output light paths 53, 54 are respectively arranged on the 1^ 立f vertical light source body. For the reflection, the positions of the two pairs of mirrors are such that two light rays forming two nearly roads are close to each other such that the two beams are broadcasted on the next scanner and then projected to the rear. The set of the same 谑 靠近 靠近 靠近 靠近 靠近 靠近 ' ' ' ' ' 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近 靠近