JP4805142B2 - 光路長が変更された異なる角度の光の合成により光学的に干渉する断層撮影におけるスペックルの減少 - Google Patents
光路長が変更された異なる角度の光の合成により光学的に干渉する断層撮影におけるスペックルの減少 Download PDFInfo
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Description
本発明は、医療診断と撮影に有用な光学撮影方法と装置に関するものである。特に、本発明は高速で角の混合を実現する方法に関する。例えば、光学的に干渉する断層撮影における画像のスペックルを減らすための光路長の変更による異なる角度の光の合成（“ＡＣＰＥ”）を実現する。
従来より、光学的に干渉する断層撮影（“ＯＣＴ”）は生物的組織の断面の高解像度画像を得る技術である。消火器と循環器系内の臨床ＯＣＴ調査によると、ＯＣＴは、うろこ状の上皮および血管の層状構造を有する様々な上皮組織の構造（＞２０μｍ）のマイクロ解剖学における画像を提供することができる。但し、バレット型食道の異形成の早期発見や動脈硬化症血小板内の炎症の識別のような医学適用の場合は、２０μｍ未満の大きさである構造の視覚化が好ましい。８〜１２μｍまで及ぶ典型的な軸解像度を得るＯＣＴシステムは、細胞核と、個々の腺と、マクロファージを含む多数の構造を撮影できる可能性を持つ。しかし、これらの物と同じ大きさの規模に発生するスペックルは、細胞核、個々の腺、およびマクロファージの包含を妨げる恐れがある。しかし、これらの物と同じ大きさの規模に発生するスペックルは、このような技術の広く普及された臨床利用に必要な細胞及び細胞小器官の組織成分の明白な識別を妨げる恐れがある。
患者の内臓でＯＣＴを行うために、カテーテルまたは内視鏡検査器具と高速画像撮影が使用される。直径を最小にするために、ほとんどのカテーテルＯＣＴ検出器は、サンプルを照射することによって組織からの信号を検出する単一の光ファイバーを使用する。ＯＣＴ画像撮影を行う時、患者の動きによって引き起こされる不具合を最小にしながら、高フレーム率（通常毎秒４−１０フレーム）とすることが好ましい。単一の光ファイバー検出器具の設計を複雑にせず、高フレーム率を維持できてＯＣＴ画像のスペックルを減らす方法があれば、それは患者の微小な組織の構造を正確に検出し、量るために有効かもしれない。
ＯＣＴ画像のスペックルの減少は前に述べた。異なった角度で得られる複数の画像の平均によってスペックルを減少させる処理を述べる（特許文献１参照）。これは角度の合成として知られている。特許文献１では、多数（Ｎ）の検出器は異なった角度から得られた画像を受け取る。それらの画像は干渉せずに平均され、信号／ノイズ率又はＳＮ率（“Ｓ
という利点がある。
また、スペックルを減らすための角度の合成に関する他の技術を述べる（特許文献２参照）。この方法では、組織に入射する光線の入射角を変えるために光線を元へ反射する反射鏡を対物レンズの前に移す。連続する画像をＮ枚得て干渉せずに加えるとスペックルは
Ｊ．Ｍ．シュミット（Ｓｃｈｍｉｔｔ）著、「光学的干渉性の顕微鏡検査のスペックルの減少のための配列の検出」、Ｐｈｙｓ．Ｍｅｄ．Ｂｉｏｌ．４２、１４２７−１４２９、１９９７年
Ｍ．バシュカンスキー（Ｂａｓｈｋａｎｓｋｙ）とＪ．レインズ（Ｒｅｉｎｔｊｅｓ）著、「光学的干渉性の断層レントゲン写真撮影のスペックルの統計量および減少」、Ｏｐｔ．Ｌｅｔｔ．２５、５４５−５４７、２０００年
本発明は、上記の課題を解決することのできるスペックル減少させる為の光路長が変更された異なる角度の光の合成による、光学的に干渉する断層撮影方法と装置を提供することを目的とする。この目的は特許請求範囲における独立項に記載の特徴の組み合わせにより達成される。また従属項は本発明の更なる有利な具体例を規定する。
本発明の一実施形態において、光路長の変更によって異なる角度の光の合成（“ＡＣＰＥ”）を使用し、この角度の光の合成を行うことによってＯＣＴ画像内のスペックルを減少させる方法を提供する。ＡＣＰＥは高速獲得を維持することができ、標準的な光学ＯＣＴカテーテルへの変更を最低限におさえる。本発明の他の実施形態では、ＡＣＰＥを使用する画像撮影のための装置を提供する。
本発明の実施形態において、サンプルを照射するカテーテルプローブ器具と方法を提供する。特に、干渉計は電磁放射の促進を進める。さらに、サンプル部は電磁放射を受け、サンプルを照射するために電磁放射から少なくとも２つの放射の生成を促進する装置を具備することができる。少なくとも２つの放射のうちの第二放射に対して少なくとも２つの放射のうちの第一の放射を遅らせるように、そのような装置を構成することができる。
本発明の他の実施形態において、基準部はさらに電磁放射を発生する。特に、干渉計は第一放射と第二放射とさらに放射を受け、これらの放射に基づいた結果の信号を発生する。第一及び第二画像が互いに異なるように、第一放射に基づく第一画像と第二放射に基づく第二画像を形成する処理装置を具備できる。さらなる画像は第一と第二画像に基づいて形成することができる。また、第一画像のノイズと第二画像のノイズと比べると、さらなる画像のノイズは小さいことがある。また、さらなる画像は次の方程式によるＳＮ率の改善が見られることがある：
ここで、ＳＮＲＡＣＰＥはＳＮ率であり、ＳＯＣＴは高率にろ過されたＯＣＴ信号の振幅であり、ｍは装置の厚さであり、ｕｉは空間的な位置で復調されたＯＣＴ信号の振幅である。そして、Ｎ＝２ｍ−１。更に、少なくとも２つの放射と関連するｍ＝２とＮ＝３画像を得ることができる。それ以外の画像は第一と第二画像の数学的な組合せに基づいて形成することもできる。
本発明の更に他の実施形態において、第一角度の第一照射と第二角度の第二放射によってサンプルを照射することができ、第一及び第二角度が互いに異なる。例えば、遅延や、第一と第二の各放射の位相と入射角の少なくとも一つに基いて、第一及び第二角度が互いに異なる。第一電磁エネルギーを検出し、検出されたエネルギーを処理装置に発射する検出器を使用することもできる。
本発明の更に他の実施形態において、装置は２つのセクションから成り、各々が第一及び第二放射を遅らせるように構成する。特に、第一放射の遅れは第二放射の遅れより大きい方が好ましい。さらに、第二放射の光路の遅れに比べて第一放射の光路の遅れは空気中少なくとも５００μｍである。更に、第二放射の光路の遅れに比べて第一放射の光路の遅れは空中少なくとも１ｍｍである。装置の屈折率は少なくとも１．５または、少なくとも３．０である。装置の表面の少なくとも一面は、シリコン且／又は反射防止塗布を含むことができる。装置は反射防止塗布されたＢＫ７ガラスでよい。ガラスの厚さは略１．６ｍｍ〜略７．７ｍｍで、屈折率は略１．５１〜略３．５である。
本発明の更に他の実施形態において、撮影する装置を提供する。装置には電磁放射を受け取るサンプル部を有する。サンプル部にはサンプルを照射するために電磁放射から少なくとも２つの放射の生成を促進する装置がある。装置は、少なくとも２つの放射の第二放射に関して少なくとも２つの放射の第一放射を遅らせるように構成されている。また、装置にはサンプル部から第一と第二放射、そして基準部から少なくとも１つの第三放射を受け取るデバイスを有し、第一と第二放射が第三放射と干渉するようになっている。更に、装置には、第一と第二と第三放射の少なくとも１つのスペクトルを周波数成分に分ける少なくとも１つのスペクトル分光装置を有し、多数の検出器から成る少なくとも１つの検出装置が具備されている。各検出器は少なくとも１つの周波数成分の少なくとも一部を検出することができる。
本発明の更に他の実施形態において、装置を提供する。装置はサンプル部に少なくとも１つの第一電磁放射を伝送する少なくとも１つの第一装置と、反射防止された基準部に少なくとも１つの第二電磁放射を有する。第一装置による放射の周波数は時間とともに変わる。サンプル部は第一電磁放射を受けて、サンプルを照射するために電磁放射から少なくとも２つの放射の生成を促進する装置を含む。装置は、少なくとも２つの放射の第二放射に関して少なくとも２つの放射の第一放射を遅らせるように構成されている。装置はさらに、サンプル部で発生する第一、第二電磁放射と基準部で発生する第二電磁放射間の干渉を検出する少なくとも１つの第二装置を含む。
本発明の更に他の実施形態において、装置を提供する。装置はサンプル部に少なくとも１つの第一電磁放射と基準部に少なくとも１つの第二電磁放射を伝送する少なくとも１つの第一装置を含む。第一、且／又は第二電磁放射のスペクトルが時間とともに変わる。スペクトルは特定時間に多数の周波数を有する。サンプル部は第一電磁放射を受けて、サンプルを照射するために電磁放射から少なくとも２つの放射の生成を促進する装置を含む。装置は、少なくとも２つの放射の第二放射に関して少なくとも２つの放射の第一放射を遅らせるように構成されている。装置はさらに、サンプル部で発生する第一、第二電磁放射と基準部で発生する第二電磁放射間の干渉を検出する少なくとも１つの第二装置を含む。
なお上記の発明の概要は、本発明の必要な特徴全てを列挙したものではなく、これらの特徴群のサブコンビネーションも又発明となりうる。
本発明の実施形態に係る方法及び装置によれば、ＯＣＴフレーム率を下げないことと、ＯＣＴ検出器に単一の受動素子を１つだけの追加は実現されるべきであるという特徴を有する。ＡＣＰＥの特徴は、患者の内部器官システムのＯＣＴ画像撮影と本発明のシステム及び方法に互換性があるようにする点である。ＡＣＰＥの実現がスペックルの減少とシステム感度間の調整を促進する一方、スペックルのノイズによって起こる問題は、現代のＯＣＴシステムより臨床診断に関して、特に１３００ｎｍの場合におそらく深刻である。ＯＣＴ画像のスペックルのノイズは２０μｍ、またそれ未満の大きさ程度の特徴の解釈の難しさを生じるため、ＡＣＰＥは、アテローム動脈硬化の異形成および炎症に限らず、重要な病気の診断のためのＯＣＴの機能をおそらく大幅に改善する。また、ＡＣＰＥは高速獲得を可能にする。
以下、本発明の実施形態について本発明を説明するが、以下の実施形態はクレームにかかる発明を限定するものではなく、又実施形態の中で説明されている特徴の組み合わせの全てが発明の解決手段に必須であるとは限らない。
＜１．材料と方法＞
図１Ａは、本発明の実施形態に係るＡＣＰＥを使用する装置を示す。光学ガラス２０は従来のＯＣＴ撮影装置５の撮影路１０に位置し、入射フィールドを、光路３０と４０にそれぞれある２つのビームレット１と２に分割する。ここでの記載において、ビームレットとは光線の一部分と定義する。光学部品により（例えば、光学ガラス２０）、入射光線の一部分（ビームレット２）はビームレット１より大きい光路長の遅れとなる。さらに、ビームレット２はビームレット１とは違う角度でサンプルを照射する。レンズを使用し、サンプル（例えば、生物組織）にビームレット１とビームレット２を集束させることができる。その結果、それぞれ異なる角度で得られたサンプル内又は上の標本の多数のＯＣＴ画像はＯＣＴ表示画面に同時に現れることがある（図１Ｂを参照）。特に、図１Ｂによると上部の画像（すなわち、１＋１と表示されたもの）が光路１（すなわち、入射と反射）から形成された画像に対応し、真中の画像（すなわち、１＋２、２＋１と表示されたもの）が光路１入射と光路２反射、そして光路２入射と光路１反射から形成された画像に対応する。更に、図１Ｂの下部の画像（すなわち、２＋２）は光路２（入射と反射）から形成された画像に対応する。
図１Ａは、本発明の実施形態に係るＡＣＰＥを使用する装置を示す。光学ガラス２０は従来のＯＣＴ撮影装置５の撮影路１０に位置し、入射フィールドを、光路３０と４０にそれぞれある２つのビームレット１と２に分割する。ここでの記載において、ビームレットとは光線の一部分と定義する。光学部品により（例えば、光学ガラス２０）、入射光線の一部分（ビームレット２）はビームレット１より大きい光路長の遅れとなる。さらに、ビームレット２はビームレット１とは違う角度でサンプルを照射する。レンズを使用し、サンプル（例えば、生物組織）にビームレット１とビームレット２を集束させることができる。その結果、それぞれ異なる角度で得られたサンプル内又は上の標本の多数のＯＣＴ画像はＯＣＴ表示画面に同時に現れることがある（図１Ｂを参照）。特に、図１Ｂによると上部の画像（すなわち、１＋１と表示されたもの）が光路１（すなわち、入射と反射）から形成された画像に対応し、真中の画像（すなわち、１＋２、２＋１と表示されたもの）が光路１入射と光路２反射、そして光路２入射と光路１反射から形成された画像に対応する。更に、図１Ｂの下部の画像（すなわち、２＋２）は光路２（入射と反射）から形成された画像に対応する。
従って、光学距離によって変更されたビームレット１と２は異なる角度でサンプルを照射する。その結果、異なる角度で得られた多数のＯＣＴ画像は単一のＯＣＴフレーム内にあることが好ましい（図１Ｂに図示）。例えば、光学部品がｍの明瞭な厚さのガラスを有し、また、それらの各光学厚さが他の光学厚さの倍数であれば、１つのＯＣＴフレームで２ｍ−１ＯＣＴ画像を得ることができる。Ｄが厚さでｎが光学材料の屈折率である場合、各画像をＤ（ｎ−１）／２というグループ遅延によって分けられる。それから明瞭なＯＣＴ画像は平均されて、随分減少したスペックルのある合成ＯＣＴ画像を形成する。画像の全てが１つのＯＣＴフレームで得られるため、単一フレーム獲得時間は維持することができる。さらに、ＯＣＴ検出器の変更は遠位光学の光路に少なくとも１つの小型光学部品の挿入を必要とするのである。ＡＣＰＥのこれらの効果は、短い直径のカテーテルまたは内視鏡内でスペックルの平均化を可能にする他、速度の獲得を可能にする点である。
以前に試しに使用した画像合成によるＯＣＴスペックル減少では、同強度のＮ画像の追
の文献ではＯＣＴのスペックル配分が確率密度関数で表されることを記述する：
ここでは、ｋ＝２ＡＲσとしてＡＲは基準電界の振幅であり、ＳＯＣＴは高率にろ過されたＯＣＴ信号の振幅、そして、σはその標準偏差である。この確率密度関数に関しては、シュミットとバシュカンスキーの文献で実験的に記載されている結果のとおり、同振幅
Ｔのサブ画像は一般的に同じ振幅を持たない可能性がある。但し、等方性後方散乱という想定で、これらのサブ画像は元のＯＣＴ画像（Ｓ０ＯＣＴ）はβ／ｍ２ほど関連している、但し、βは明瞭なサブ画像に携わる光路長の組合せの数である。この結果、ＡＣＰＥのＳＮＲは次のように定義する：
ここでは、μｉは空間的な位置における復調されたＯＣＴ信号の振幅であり、そして、Ｎ＝２ｍ−１。ｍ＝２の場合、Ｎ＝３画像は得られ、ＡＣＰＥ ＯＣＴのサブ画像の振幅間の関係はＳ１ＯＣＴ＝Ｓ３ＯＣＴ＝１／４Ｓ０ＯＣＴ、及び、Ｓ２ＯＣＴ＝２Ｓ１ＯＣＴ＝１／２Ｓ０ＯＣＴである。すると、混合されたｍ＝２ＡＣＰＥ画像のＳＮＲの改善の可能性は、ＳＮＲ０がＳ０ＯＣＴのＳＮ率であると、ＳＮＲＡＣＰＥ／ＳＮＲ０＝１．６３である。
＜２．例１＞
本発明において、多偏光ＯＣＴシステムはＡＣＰＥを実現する装置を利用できる（例えば、図１Ａに図示）。本発明に係るこのようなシステムを使用すると、ＯＣＴ画像は毎秒２フレーム（例えば、５００軸画素×５００横画素）で得ることができ、反対にしたグレー・スケール・テーブルで表示し、デジタル保管できる。このようにＯＣＴシステムに使用できる光源を中心波長が１３１０ｎｍで帯域幅が７０ｎｍとし、これによって、組織内の軸解像度を略８μｍで提供できる。
本発明において、多偏光ＯＣＴシステムはＡＣＰＥを実現する装置を利用できる（例えば、図１Ａに図示）。本発明に係るこのようなシステムを使用すると、ＯＣＴ画像は毎秒２フレーム（例えば、５００軸画素×５００横画素）で得ることができ、反対にしたグレー・スケール・テーブルで表示し、デジタル保管できる。このようにＯＣＴシステムに使用できる光源を中心波長が１３１０ｎｍで帯域幅が７０ｎｍとし、これによって、組織内の軸解像度を略８μｍで提供できる。
変更された手持ち式の検流計検出器は（例えば、図１Ａの装置）、ＯＣＴ撮影装置５のサンプル部に挿入できる。対物レンズ５０は２５ｍｍの焦点距離および０．１１の開口数値（ＮＡ）を有し、２３μｍに及ぶ１／ｅ２焦点直径を有する。正方形型の反射防止塗布したＤ＝３．１ｍｍのＢＫ７ガラスを（ｎ＝１．５１）（例えば、光学ガラス２０）、照明光線の半分と重なるように光ファイバーのコリメーターと対物レンズ５０の間に挿入できる（図１Ａ参照）。この構成で略８００μｍのＯＣＴ画像を分けることができる。ガラス板が挿入されると、ガラス端と垂直な焦点の直径は２倍（４６μｍ）増加する可能性がある。しかし、ＯＣＴ画像の平面では横断解像度は維持される。
＜３．例２＞
１％の内部脂肪溶液と寒天から成っている固体ファントムを使用して、ＡＣＰＥによりスペックル減少を測定することができる。例えば、４本の毛をゼリー状の内部脂肪・寒天内に異なった横断位置、且深さに埋め込むことができる。図２Ａは、内部脂肪の略図である。図２Ｂと２Ｃは、ＢＫ７ガラス板がある場合とない場合の対応するＯＣＴ画像である。１〜５と表示したＲＯＩは、ＡＣＰＥでＳＮＲ改善を測定する位置を表す。ＢＫ７ガラス板２０（３．１ｍｍのＢＫ７ガラス部品がある）をサンプル部に挿入すると、元のＯＣＴ画像（図２Ｃ参照）のコピーが３枚形成され、これらの各画像は異なった照明角度で得られ、グループ遅延の増加、例えば８００μｍ、によって分かれている。図２Ｃの上部及び下部の画像にある信号の振幅は、中央の画像のおよそ半分である（Ｓ１ＯＣＴ／Ｓ２ＯＣＴ＝Ｓ３ＯＣＴ／Ｓ２ＯＣＴ＝１：２）。図２（Ｄ）で示す合成されたＡＣＰＥの画像は、図２Ｃに示す３つの画像を干渉がなく平均することによって得ることができる。図２（Ｄ）では、多くのスペックルが減少した合成画像を見ることができる。元のＯＣＴ画像と比較すると、図２Ｂに図示す５つの領域ＡＣＰＥ ＳＮＲ改善の平均は、好ましくは１．５４±０．１２（平均±標準偏差）である。
１％の内部脂肪溶液と寒天から成っている固体ファントムを使用して、ＡＣＰＥによりスペックル減少を測定することができる。例えば、４本の毛をゼリー状の内部脂肪・寒天内に異なった横断位置、且深さに埋め込むことができる。図２Ａは、内部脂肪の略図である。図２Ｂと２Ｃは、ＢＫ７ガラス板がある場合とない場合の対応するＯＣＴ画像である。１〜５と表示したＲＯＩは、ＡＣＰＥでＳＮＲ改善を測定する位置を表す。ＢＫ７ガラス板２０（３．１ｍｍのＢＫ７ガラス部品がある）をサンプル部に挿入すると、元のＯＣＴ画像（図２Ｃ参照）のコピーが３枚形成され、これらの各画像は異なった照明角度で得られ、グループ遅延の増加、例えば８００μｍ、によって分かれている。図２Ｃの上部及び下部の画像にある信号の振幅は、中央の画像のおよそ半分である（Ｓ１ＯＣＴ／Ｓ２ＯＣＴ＝Ｓ３ＯＣＴ／Ｓ２ＯＣＴ＝１：２）。図２（Ｄ）で示す合成されたＡＣＰＥの画像は、図２Ｃに示す３つの画像を干渉がなく平均することによって得ることができる。図２（Ｄ）では、多くのスペックルが減少した合成画像を見ることができる。元のＯＣＴ画像と比較すると、図２Ｂに図示す５つの領域ＡＣＰＥ ＳＮＲ改善の平均は、好ましくは１．５４±０．１２（平均±標準偏差）である。
＜４．例３＞
ＳＮＲの改善を生体内で論証するためには、ＡＣＰＥ ＯＣＴ撮影を患者の前腕の腹部で行うことができる。図３Ａと３Ｂは、代表的な一組の画像を示す。図３Ａは、ＢＫ７ ＡＣＰＥ部品の挿入前に生体内で得た前腕の腹部のＯＣＴ画像を示す。これらの映像の視覚的な判定によると、合成されたＡＣＰＥの画像（図３Ｂ）の質的な改善が明らかである。表皮（Ｅ）と皮膚（Ｄ）の間にある境界は、図３Ｂで示すように、ＡＣＰＥを利用した方が明確に表れる。さらに、真皮脈管構造と一致する横の構造は図３ＢのＡＣＰＥ画像で容易に識別される。図３Ｂにある元のＯＣＴ画像とＡＣＰＥのＳＮＲを測定することができ、１．５６というＳＮＲの改善ができる。
ＳＮＲの改善を生体内で論証するためには、ＡＣＰＥ ＯＣＴ撮影を患者の前腕の腹部で行うことができる。図３Ａと３Ｂは、代表的な一組の画像を示す。図３Ａは、ＢＫ７ ＡＣＰＥ部品の挿入前に生体内で得た前腕の腹部のＯＣＴ画像を示す。これらの映像の視覚的な判定によると、合成されたＡＣＰＥの画像（図３Ｂ）の質的な改善が明らかである。表皮（Ｅ）と皮膚（Ｄ）の間にある境界は、図３Ｂで示すように、ＡＣＰＥを利用した方が明確に表れる。さらに、真皮脈管構造と一致する横の構造は図３ＢのＡＣＰＥ画像で容易に識別される。図３Ｂにある元のＯＣＴ画像とＡＣＰＥのＳＮＲを測定することができ、１．５６というＳＮＲの改善ができる。
本発明の実施形態に係る装置と方法はＯＣＴフレーム率を下げず、ＯＣＴ検出器への最小限な変更を必要としながら、ＯＣＴ画像のスペックルの減少を提供する。ＡＣＰＥの実現はスペックルの減少と３つの他のＯＣＴシステム・パラメータの間の調整をする、すなわちａ）サンプル部の横断解像度と、ｂ）基準部光路の総距離と、ｃ）ＯＣＴ画像の感度。特に、どの対物レンズに関しても、ＡＣＰＥは各ビームレットのレンズ口径をアンダフィルすることによって、１次元の横断解像度を低下することがある。ほとんどの場合、この解像度の損失は対物レンズの開口数値（ＮＡ）を増加することによって償うことができる。
スペックルを平均したＡＣＰＥ−ＯＣＴ画像は、ほぼ同じ周波数で基準部光路の距離の増加した遅れをスキャンすることによって従来のＯＣＴ画像と同じ率で得ることができる。各ＯＣＴサブ画像を得るためには、ＬをＯＣＴシステムの元のスキャンの長さとした場合、ＡＣＰＥ−ＯＣＴシステムの新しいスキャンの長さは、好ましくはＬ＝（２ｍ−１）である。位相制御ＲＳＯＤ線を使用することによって、スキャンが１０ｍｍ範囲まで可能であり、従って、ｍ＝３と、Ｌ＝２ｍｍと、最大、予測ＳＮＲ改善がおよそ〜２．１を可能とする。
スキャン率を維持している間基準部の光路長スキャン範囲を広げることは、電子帯域幅を増加し、ＯＣＴシステムの感度を減らす可能性がある。また、ＡＣＰＥがサンプル部力を２ｍ−１のサブ画像に分割するので、各サブ画像は元のサンプル部力の一部分を含む。人間の組織を撮影する場合、これらの損失はＯＣＴ画像の浸透深さに影響を及ぼす可能性がある。バレット型食道やアテローム動脈硬化プラークの大食細胞を持つ患者の細胞核を例として、臨床関連性の多くの特徴は、ｍが適度な場合、組織の表面にあるためＡＣＰＥが提供する画像の質の改善はおそらく感度の損失を上回る。さらに、より有能な干渉計の設計と高い発電の技術的な開発が進歩するため、臨床的に実用可能なＯＣＴの源はＡＣＰＥの感度の損失が無いに等しいとする可能性がある。
上述した例（３．１ｍｍＢＫ７）でここに記載した光路長変更の光学部品の厚さは、個々のサブ画像間に８００μｍの分かれを引き起こすため、ある組織のＯＣＴ画像撮影が十分でないことがある。ＢＫ７ガラスの厚さを７．７ｍｍに厚くすることによって、光路長の分離を２ｍｍにする可能性がある。この厚さは自由空間で手持ち式型のＯＣＴ検出器に相応しいかもしれないが、固定の長さを最小にすることが重要である短い直径の柔軟なカテーテルの場合に問題となる。光路長の変更の光学部品の厚さを厚くするためには、シリコン（ｎ＝３．５）のようなより高い屈折率材料を使用することがある。シリコンで２ｍｍの遅れを生じるためには、材料の略１．６ｍｍを使用することが好ましい。高い屈折率ガラスを使用した場合、基準部とサンプル部の間の散乱の不均衡は考慮されるべきである。高解像度のＯＣＴ画像撮影（Δλ／λ＞１０％）のために、光路長の変更に使用する光学材料の適切な選択は源の中心の波長と帯域幅に左右される。
以上、本発明を実施形態を用いて説明したが、本発明の技術的範囲は上記実施形態に記載の範囲には限定されない。上記実施形態に、多様な変更又は改良を加えることが出来る。そのような変更又は改良を加えた形態も本発明の技術的範囲に含まれ得ることが、特許請求の範囲から明らかである。
１ ビームレット
２ ビームレット
５ ＯＣＴ撮影装置
１０ 撮影路
２０ 光学ガラス
３０ 光路
４０ 光路
５０ 対物レンズ
２ ビームレット
５ ＯＣＴ撮影装置
１０ 撮影路
２０ 光学ガラス
３０ 光路
４０ 光路
５０ 対物レンズ
Claims (9)
- サンプルを照射する装置は、
ａ）電磁放射を送る干渉計と、
ｂ）前記サンプルを照射するため、そして少なくとも２つの放射のうちの第二放射に対して少なくとも２つの放射のうちの第一放射を遅らせるために、前記電磁放射を受け取り、該電磁放射から少なくとも２つの放射を生成するための装置を包含する、サンプル部と、
ｃ）さらなる電磁放射を提供し、そこでは、前記干渉計が、前記第一と前記第二とさらなる放射を受け取り、該第一と該第二と該さらなる放射に基づく合成信号を形成する基準部と、
ｄ）前記第一放射に基づく第一画像、前記合成信号に基づく第二画像、及び前記第一と前記第二の画像に基づくさらなる画像を形成する、処理装置と、を有し、
前記処理装置では、該第一と該第二画像が互いに異なっており、
前記処理装置は、前記第一及び前記第二画像に基づいて、さらなる画像を形成し、
前記さらなる画像は、下記の方程式に従って改善されるＳＮ率の信号を有することを特徴とするサンプルを照射する装置。
- 請求項１に記載のサンプルを照射する装置において、
前記さらなる画像に、前記第一画像のノイズ及び前記第二画像のノイズより小さいノイズがあることを特徴とするサンプルを照射する装置。 - 請求項１に記載のサンプルを照射する装置において、
少なくとも２つの放射と関連してｍ＝２でＮ＝３の画像が得られることを特徴とするサンプルを照射する装置。 - 請求項１に記載のサンプルを照射する装置において、
前記さらなる画像は前記第一及び前記第二画像の数学的な組合せに基づいて形成されることを特徴とするサンプルを照射する装置。 - 請求項１に記載のサンプルを照射する装置において、
互いに異なる第一及び第二角度であって、前記サンプルは前記第一角度では前記第一放射によって照射され、該サンプルは前記第二角度では前記第二放射に照射されることを特徴とするサンプルを照射する装置。 - 請求項５に記載のサンプルを照射する装置において、
前記第一及び前記第二角度は、遅延、及び位相又はそれぞれの入射角の少なくとも一方に応じて、互いに異なることを特徴とするサンプルを照射する装置。 - 請求項１に記載のサンプルを照射する装置において、
さらに第一の電磁エネルギーを検出する検出器から成り、この検出器は、前記検出されたエネルギーを前記処理装置に伝送することを特徴とするサンプルを照射する装置。 - 請求項１に記載のサンプルを照射する装置において、
前記第一放射の遅れが前記第二放射の遅れより大きいもので、前記少なくとも２つの放射を生成するための装置は、該第一及び該第二放射のそれぞれの１つを遅らせるように各セクションが構成される２つのセクションを具備することを特徴とするサンプルを照射する装置。 - 画像撮影する装置は、
ａ）サンプルを照射するため、そして少なくとも２つの放射のうちの第二放射に対して少なくとも２つの放射のうちの第一放射を遅らせるために、前記電磁放射を受け取り、該電磁放射から少なくとも２つの放射を生成するための装置を包含する、サンプル部と、
ｂ）前記第一及び前記第二放射は第三放射を干渉し、前記サンプル部からの該第一、該第二放射と基準部からの少なくとも１つの第三放射を受け取るデバイスと、
ｃ）前記第一と前記第二と前記第三放射の少なくとも１つのスペクトルを周波数成分に分け、前記サンプル部と協働する少なくとも１つの分光分離装置と、
ｄ）各検出器が少なくとも１つの周波数の一部を検出することができる複数の検出器を含む少なくとも１つの検出装置と、
ｅ）さらなる電磁放射を提供し、そこでは、前記干渉計が、前記第一と前記第二とさらなる放射を受け取り、該第一と該第二と該さらなる放射に基づく合成信号を形成する基準部と、
ｆ）前記第一放射に基づく第一画像、前記合成信号に基づく第二画像、及び前記第一と前記第二の画像に基づくさらなる画像を形成する、処理装置と、を有し、
前記処理装置では、該第一と該第二画像が互いに異なっており、
前記処理装置は、前記第一及び前記第二画像に基づいて、さらなる画像を形成し、
前記さらなる画像は、下記の方程式に従って改善されるＳＮ率の信号を有することを特徴とする画像撮影する装置。
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| PCT/US2004/010152 WO2004088361A2 (en) | 2003-03-31 | 2004-03-31 | Speckle reduction in optical coherence tomography by path length encoded angular compounding |
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Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2001038820A1 (de) * | 1999-11-24 | 2001-05-31 | Haag-Streit Ag | Verfahren und vorrichtung zur messung optischer eigenschaften wenigstens zweier voneinander distanzierter bereiche in einem transparenten und/oder diffusiven gegenstand |
| WO2001042735A1 (en) * | 1999-12-09 | 2001-06-14 | Oti Ophthalmic Technologies Inc. | Optical mapping apparatus with adjustable depth resolution |
| JP2003516531A (ja) * | 1999-12-09 | 2003-05-13 | オーティーアイ オフサルミック テクノロジーズ インク | 可変奥行き解像力を有する光学マッピング装置 |
| JP2001272331A (ja) * | 2000-03-24 | 2001-10-05 | Japan Science & Technology Corp | 空間遅延型フィゾー干渉計 |
Also Published As
| Publication number | Publication date |
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| JP2011209293A (ja) | 2011-10-20 |
| US20060227333A1 (en) | 2006-10-12 |
| WO2004088361A2 (en) | 2004-10-14 |
| AU2004225188A1 (en) | 2004-10-14 |
| EP1611470A4 (en) | 2009-06-17 |
| US20100157309A1 (en) | 2010-06-24 |
| US8174702B2 (en) | 2012-05-08 |
| EP2436307A1 (en) | 2012-04-04 |
| WO2004088361A3 (en) | 2005-04-07 |
| EP1611470A2 (en) | 2006-01-04 |
| US20130314716A1 (en) | 2013-11-28 |
| CA2519937C (en) | 2012-11-20 |
| JP5571621B2 (ja) | 2014-08-13 |
| JP2006522341A (ja) | 2006-09-28 |
| EP2436307B1 (en) | 2015-10-21 |
| CA2519937A1 (en) | 2004-10-14 |
| US20120281237A1 (en) | 2012-11-08 |
| US9226665B2 (en) | 2016-01-05 |
| AU2004225188B2 (en) | 2010-04-15 |
| EP1611470B1 (en) | 2015-10-14 |
| US8559012B2 (en) | 2013-10-15 |
| US7567349B2 (en) | 2009-07-28 |
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