JP2010082370A - Brain function measurement instrument - Google Patents
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本発明は、電磁波を用いた脳機能計測装置に関する。 The present invention relates to a brain function measuring apparatus using electromagnetic waves.
従来、生体組織に対して透過性が高い近赤外光を用いて、生体組織における血流変化を検出することが行われている。 Conventionally, detection of a change in blood flow in a living tissue has been performed using near-infrared light that is highly permeable to the living tissue.
例えば、特許文献１及び２には、近赤外光を頭部や筋肉などの生体組織に向けて照射し、生体組織を透過した近赤外光を分析することで、生体組織を流れる血液中のヘモグロビン酸素化状態の変化を調べる方法が開示されている。 For example, Patent Documents 1 and 2 disclose that in a blood flowing through a living tissue, near infrared light is irradiated toward a living tissue such as a head or muscle, and the near infrared light transmitted through the living tissue is analyzed. A method for investigating changes in the hemoglobin oxygenation state is disclosed.
この方法は、生体組織の透過時における近赤外光の光吸収量を測定することで、血流の増加に伴い生じる酸素化ヘモグロビンの増加と脱酸素化ヘモグロビンの減少を観測するものであって、一般に近赤外分光法(ＮＩＲＳ：Ｎｅａｒ−Ｉｎｆｒａｒｅｄ Ｓｐｅｃｔｒｏｓｃｏｐｙ）と呼ばれ、非浸襲的な実施が可能であるため、安全な手法として知られている。 This method measures the increase in oxygenated hemoglobin and the decrease in deoxygenated hemoglobin caused by an increase in blood flow by measuring the amount of light absorbed by near-infrared light during transmission through living tissue. In general, it is called near-infrared spectroscopy (NIRS) and is known as a safe technique because it can be implemented non-invasively.
図３は、近赤外分光法により大脳皮質における活動を検出する従来の脳機能計測装置４０を示している。この脳機能計測装置４０は、頭皮２上に設けた光源４１から脳５に近赤外光Ｌを照射して、この照射により生じた反射光および散乱光を、頭皮２上に設けた受光器４２によって受光することで、脳５の血流変化（血液中のヘモグロビン酸素化状態の変化）を検出するようになっている。 FIG. 3 shows a conventional brain function measuring apparatus 40 that detects activity in the cerebral cortex by near infrared spectroscopy. The brain function measuring device 40 irradiates the brain 5 with near-infrared light L from a light source 41 provided on the scalp 2, and receives a reflected light and scattered light generated by the irradiation on the scalp 2. By receiving light by 42, a change in blood flow in the brain 5 (change in oxygenated state of hemoglobin in the blood) is detected.
ところで図３に示す脳機能計測装置４０では、脳５の構造が複雑であるため、受光器４２が受光した光の経路を特定することができない。このため、図３に示す脳機能計測装置４０では、脳５における活動部位を高精度に特定することが困難である。 By the way, in the brain function measuring apparatus 40 shown in FIG. 3, since the structure of the brain 5 is complicated, the path | route of the light which the light receiver 42 received cannot be specified. For this reason, in the brain function measuring device 40 shown in FIG. 3, it is difficult to specify the active site in the brain 5 with high accuracy.
また、大脳皮質５０の血流変化を計測するためには、光源４１と受光器４２とを３０ｍｍ程度間隔をあけて配置する必要がある。このため、受光器４２を高密度に配置できないため、高い空間分解能を得ることができない。 Moreover, in order to measure the blood flow change of the cerebral cortex 50, it is necessary to arrange the light source 41 and the light receiver 42 with an interval of about 30 mm. For this reason, since the light receivers 42 cannot be arranged with high density, high spatial resolution cannot be obtained.
本発明はこうした状況に鑑みてなされたものであり、その目的は、脳の活動部位を高精度に特定できるとともに、高い空間分解能が得られる脳機能計測装置を提供することである。 The present invention has been made in view of such circumstances, and an object of the present invention is to provide a brain function measuring apparatus that can specify an active site of the brain with high accuracy and obtain high spatial resolution.
本発明の脳機能計測装置は、脳に向けて電磁波を出射する電磁波発生手段と、脳を透過した前記電磁波を検出する電磁波検出手段とを備え、前記電磁波検出手段は、頭皮上に設けられ、前記電磁波発生手段は、前記電磁波検出手段と脳を介して反対側に設けられることを特徴とする。 The brain function measuring device of the present invention comprises an electromagnetic wave generating means for emitting an electromagnetic wave toward the brain, and an electromagnetic wave detecting means for detecting the electromagnetic wave transmitted through the brain, the electromagnetic wave detecting means being provided on the scalp, The electromagnetic wave generating means is provided on the opposite side of the electromagnetic wave detecting means via the brain.
好ましくは、前記電磁波発生手段は、前記電磁波としての近赤外光を脳に向けて出射する光源であり、前記電磁波検出手段は、脳を透過した前記近赤外光を受光する受光器アレイであることを特徴とする。 Preferably, the electromagnetic wave generating means is a light source that emits near infrared light as the electromagnetic wave toward the brain, and the electromagnetic wave detecting means is a light receiver array that receives the near infrared light transmitted through the brain. It is characterized by being.
好ましくは、前記電磁波発生手段は、前記電磁波としてのテラヘルツ波を脳に向けて出射するテラヘルツ波発生装置であり、前記電磁波検出手段は、脳を透過した前記テラヘルツ波を検出する検出器であることを特徴とする。 Preferably, the electromagnetic wave generation means is a terahertz wave generation device that emits terahertz waves as the electromagnetic waves toward the brain, and the electromagnetic wave detection means is a detector that detects the terahertz waves that have passed through the brain. It is characterized by.
好ましくは、前記電磁波発生手段は、口腔内に配置されることを特徴とする。 Preferably, the electromagnetic wave generating means is arranged in the oral cavity.
好ましくは、前記電磁波発生手段は、鼻腔内に配置されることを特徴とする。 Preferably, the electromagnetic wave generating means is arranged in the nasal cavity.
好ましくは、前記電磁波発生手段は、一つ設けられることを特徴とする。 Preferably, one electromagnetic wave generating means is provided.
好ましくは、前記電磁波検出手段は、前記頭皮上の異なる位置に複数設けられることを特徴とする。 Preferably, a plurality of the electromagnetic wave detection means are provided at different positions on the scalp.
好ましくは、前記電磁波発生手段には、前記電磁波の出射方向を調整する光ファイバが設けられることを特徴とする。 Preferably, the electromagnetic wave generating means is provided with an optical fiber that adjusts an emission direction of the electromagnetic wave.
好ましくは、前記光ファイバの出射部には、前記電磁波を放射状に拡散する球面状のレンズが設けられることを特徴とする。 Preferably, the emitting portion of the optical fiber is provided with a spherical lens that diffuses the electromagnetic waves radially.
本発明によれば、電磁波検出手段を頭皮上に設け、電磁波発生手段を電磁波検出手段と脳を介して反対側に設けるようにしたことから、電磁波検出手段で受光される電磁波には、脳への照射で反射した電磁波はほとんど含まれず、脳を透過した電磁波が大部分となる。また、感覚や運動等の機能を司る大脳皮質は脳の表面近くにあり、電磁波検出手段で検出される電磁波には電磁波検出手段から近い距離にある大脳皮質での血流変化が反映される。これにより、脳の活動部位を高精度に特定することができる。 According to the present invention, the electromagnetic wave detection means is provided on the scalp, and the electromagnetic wave generation means is provided on the opposite side of the electromagnetic wave detection means and the brain. The electromagnetic wave reflected by the irradiation is hardly included, and the electromagnetic wave transmitted through the brain is mostly. The cerebral cortex that controls functions such as sensation and movement is close to the surface of the brain, and the electromagnetic wave detected by the electromagnetic wave detection means reflects a change in blood flow in the cerebral cortex at a short distance from the electromagnetic wave detection means. Thereby, the active site | part of a brain can be pinpointed with high precision.
また上述の電磁波検出手段と電磁波発生手段との位置関係により、電磁波検出手段を電磁波発生手段による制限なく配置することができる。このため、電磁波検出手段を高密度に配置することができるため、高い空間分解能を得ることができる。 Further, the electromagnetic wave detecting means can be arranged without limitation by the electromagnetic wave generating means due to the positional relationship between the electromagnetic wave detecting means and the electromagnetic wave generating means. For this reason, since electromagnetic wave detection means can be arranged with high density, high spatial resolution can be obtained.
以下、この発明の実施の形態について図面を参照しながら詳細に説明する。なお、図中同一または相当部分には同一符号を付し、その説明は繰り返さない。 Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. In the drawings, the same or corresponding parts are denoted by the same reference numerals, and description thereof will not be repeated.
図１は、本発明の実施の形態における脳機能計測装置１を示している。脳機能計測装置１は、頭皮２上に設けられた複数の受光器アレイ３と、口腔４内に配置されることで受光器アレイ３と脳５を介して反対側に設けられた、一つの光源６とを備えている。 FIG. 1 shows a brain function measuring apparatus 1 according to an embodiment of the present invention. The brain function measuring device 1 includes a plurality of light receiver arrays 3 provided on the scalp 2 and a single one provided on the opposite side via the light receiver array 3 and the brain 5 by being disposed in the oral cavity 4. And a light source 6.
各受光器アレイ３は、頭皮２上の異なる位置に設けられており、直径が１ｃｍ程度の受光面を有し、該受光面に受光された光の強度を計測可能である。 Each light receiver array 3 is provided at a different position on the scalp 2, has a light receiving surface with a diameter of about 1 cm, and can measure the intensity of light received by the light receiving surface.
図２は、光源６を拡大して示す概略図である。光源６は、例えば、近赤外光Ｌを発生させる発生部７と、発生部７で発生した近赤外光Ｌの出射方向を調整する光ファイバ８とによって構成される。光ファイバ８は、近赤外光Ｌが脳５に向けて出射されるように、出射部９の向きが調整される。また、光ファイバ８の出射部９には球面状のレンズ１０が取り付けられ、レンズ１０は、出射部９から出射した近赤外光Ｌを放射状に拡散する。 FIG. 2 is a schematic view showing the light source 6 in an enlarged manner. The light source 6 includes, for example, a generation unit 7 that generates near-infrared light L and an optical fiber 8 that adjusts the emission direction of the near-infrared light L generated by the generation unit 7. In the optical fiber 8, the direction of the emitting portion 9 is adjusted so that the near-infrared light L is emitted toward the brain 5. A spherical lens 10 is attached to the emitting portion 9 of the optical fiber 8, and the lens 10 diffuses the near infrared light L emitted from the emitting portion 9 radially.
以上の構成を有する脳機能計測装置１によれば、口腔４内に配置された光源６から、脳５に向けて近赤外光Ｌが出射されることで、近赤外光Ｌは、脳５内を上方へ進行して、脳５の頭皮２近傍に位置する大脳皮質５０を透過する。この際、光源６から出射された近赤外光Ｌは、レンズ１０により放射状に拡散されることで大脳皮質５０のあらゆる位置を透過し、大脳皮質５０の血液中のヘモグロビンに吸収される。そして、大脳皮質５０を透過した各近赤外光Ｌは、その進行方向の先に存在する受光器アレイ３に受光されて、大脳皮質５０の透過後における強度が計測される。そして、この計測された強度と光源６からの出射時における強度との差から、近赤外光Ｌの大脳皮質５０透過時における吸収量が得られ、この吸収量に基づき、大脳皮質５０の血流変化（大脳皮質５０における血液中のヘモグロビン酸素化状態）が観測される。 According to the brain function measuring apparatus 1 having the above configuration, the near-infrared light L is emitted from the light source 6 disposed in the oral cavity 4 toward the brain 5, so that the near-infrared light L is Proceeds upward in 5 and passes through the cerebral cortex 50 located in the vicinity of the scalp 2 of the brain 5. At this time, the near-infrared light L emitted from the light source 6 is diffused radially by the lens 10 so as to pass through any position of the cerebral cortex 50 and absorbed by hemoglobin in the blood of the cerebral cortex 50. And each near-infrared light L which permeate | transmitted the cerebral cortex 50 is received by the light receiver array 3 which exists ahead of the advancing direction, and the intensity | strength after the permeation | transmission of the cerebral cortex 50 is measured. Then, from the difference between the measured intensity and the intensity at the time of emission from the light source 6, the amount of absorption of the near-infrared light L when transmitted through the cerebral cortex 50 is obtained. Based on this amount of absorption, the blood of the cerebral cortex 50 A flow change (hemoglobin oxygenation state in blood in the cerebral cortex 50) is observed.
本実施の形態では、受光器アレイ３を頭皮２上に配置し、光源６を、受光器アレイ３と脳５を介する反対側に設けるようにしたことから、受光器アレイ３で受光される近赤外光Ｌには、脳５への照射により生じた反射光はほとんど含まれず、脳５を透過した近赤外光Ｌが大部分となる。近赤外光Ｌの吸収が検出された受光器アレイ３（出射時における強度よりも低い強度が計測された受光器アレイ３）が存在する場合には、その受光器アレイ３と近い大脳皮質５０の部位に血流変化が生じていると判断できる。これにより、脳５の活動部位を特定することができる。 In the present embodiment, the light receiver array 3 is arranged on the scalp 2 and the light source 6 is provided on the opposite side of the light receiver array 3 and the brain 5. The infrared light L includes almost no reflected light generated by irradiation of the brain 5, and most of the near-infrared light L transmitted through the brain 5. When there is a light receiver array 3 in which the absorption of the near-infrared light L is detected (a light receiver array 3 whose intensity is lower than the intensity at the time of emission), the cerebral cortex 50 close to the light receiver array 3 is present. It can be determined that a change in blood flow has occurred in the region. Thereby, the active site of the brain 5 can be specified.
また、受光器アレイ３が配置される頭皮２上には光源６を設けないことから、受光器アレイ３を、光源６による制限を受けることなく配置することができる。これにより、受光器アレイ３を高密度に配置することができるため、高い空間分解能を得ることができる。 In addition, since the light source 6 is not provided on the scalp 2 where the light receiver array 3 is disposed, the light receiver array 3 can be disposed without being restricted by the light source 6. Thereby, since the light receiver array 3 can be arrange | positioned with high density, high spatial resolution can be obtained.
また、受光器アレイ３を光源６による制限なく配置できるため、高い感度を有する大型の受光器アレイ３を使用することができる。これにより、脳５透過後の近赤外光Ｌを漏れなく受光器アレイ３に受光させることができるため、脳５のあらゆる位置で生じた活動を検出することができる。 Moreover, since the light receiver array 3 can be arranged without limitation by the light source 6, a large light receiver array 3 having high sensitivity can be used. Thereby, since the near-infrared light L after passing through the brain 5 can be received by the light receiver array 3 without omission, it is possible to detect the activity occurring at any position of the brain 5.
また、受光器アレイ３を頭皮２上に配置することで、頭皮２に近い位置に存在する大脳皮質５０で生じた光吸収が鮮鋭に検出される。このため、感覚、運動、思考、記憶など高次機能を司る大脳皮質５０における血流変化を的確に計測することができる。 In addition, by arranging the light receiver array 3 on the scalp 2, light absorption generated in the cerebral cortex 50 located near the scalp 2 is sharply detected. For this reason, the blood flow change in the cerebral cortex 50 that controls higher-order functions such as sensation, movement, thought, and memory can be accurately measured.
また、光源６を口腔４内に配置することで、高強度の近赤外光Ｌを発する大型の光源６を使用することができる。このため、脳５の透過に十分な強度を有する近赤外光Ｌを、脳５に向けて照射することができる。これにより、脳５透過後の近赤外光Ｌが受光器アレイ３において確実に検出されるため、脳５の活動を確実に捉えることができる。 Moreover, the large sized light source 6 which emits the high intensity | strength near-infrared light L can be used by arrange | positioning the light source 6 in the oral cavity 4. FIG. For this reason, it is possible to irradiate the brain 5 with near-infrared light L having sufficient intensity for transmission through the brain 5. Thereby, since the near-infrared light L after passing through the brain 5 is reliably detected in the light receiver array 3, the activity of the brain 5 can be reliably captured.
また、光源６を口腔４内に配置することで、非浸襲で、光源６を取り付けることができる。このため、光源６の取り付けが容易且つ安全に行われる。 Moreover, by arranging the light source 6 in the oral cavity 4, the light source 6 can be attached in a non-invasive manner. For this reason, the light source 6 can be easily and safely attached.
また、光源６が配置される口腔４は脳５に近い位置に存在するために、近赤外光Ｌが脳５に至る過程で生じる光吸収を小さく抑えることができる。これにより、脳５に高強度の近赤外光Ｌを照射することや、脳５における正確な光吸収量を測定する上で有利になる。 Moreover, since the oral cavity 4 in which the light source 6 is disposed is located near the brain 5, light absorption generated in the process in which the near-infrared light L reaches the brain 5 can be suppressed to a low level. This is advantageous in irradiating the brain 5 with high-intensity near-infrared light L and measuring the exact amount of light absorption in the brain 5.
また、口腔４の壁面を構成する口蓋表面は滑らかであるために、光源６を口腔４内に配置するにあたって、光源６を口蓋表面に密着させることができる。これにより、光の漏れを小さくすることができるため、近赤外光Ｌが脳５に至る過程で生じる光吸収を、さらに一層小さく抑えることができる。 Moreover, since the palate surface which comprises the wall surface of the oral cavity 4 is smooth, when arrange | positioning the light source 6 in the oral cavity 4, the light source 6 can be stuck to the palate surface. Thereby, since the leakage of light can be reduced, light absorption that occurs in the process in which the near-infrared light L reaches the brain 5 can be further reduced.
また、光源６を口腔４内に配置することで、近赤外光Ｌに外部から加えられる光ノイズを軽減させることができる。 Moreover, by arranging the light source 6 in the oral cavity 4, optical noise applied from the outside to the near infrared light L can be reduced.
また、光ファイバ８によって近赤外光Ｌの出射方向を調整するようにしたことから、近赤外光Ｌを確実に脳５へ照射することができる。また光ファイバ８の出射部９に設けたレンズ１０により、近赤外光Ｌを放射状に拡散するようにしたので、脳５のあらゆる位置に近赤外光Ｌを透過させることができる。これにより、さらに高い空間分解能が得られる。 Moreover, since the emission direction of the near infrared light L is adjusted by the optical fiber 8, the near infrared light L can be reliably irradiated to the brain 5. Further, since the near infrared light L is diffused radially by the lens 10 provided at the emitting portion 9 of the optical fiber 8, the near infrared light L can be transmitted to any position of the brain 5. Thereby, higher spatial resolution can be obtained.
また、光源６を一つのみ設けていることで、脳機能計測装置１のハードウェア構成は簡易になる。 Further, by providing only one light source 6, the hardware configuration of the brain function measuring apparatus 1 is simplified.
なお、本発明は、上記の実施形態に限られず、種々改変することができる。 The present invention is not limited to the above-described embodiment, and various modifications can be made.
例えば、光源６は鼻腔１２（図１参照）内に配置されてもよい。このようにしても、光源６は、非浸襲で、容易且つ安全に人体に取り付けられる。また光源６が口腔４内に配置される場合に比して、より脳５に近い位置に光源６が配置されるので、近赤外光Ｌが脳５に至るまでの過程で生じる光吸収を小さく抑えることができる。これにより、小型の光源６を使用したとしても、適当な強度の近赤外光Ｌが受光器アレイ３において検出される。 For example, the light source 6 may be disposed in the nasal cavity 12 (see FIG. 1). Even in this case, the light source 6 is non-invasive and can be easily and safely attached to the human body. In addition, since the light source 6 is disposed closer to the brain 5 than when the light source 6 is disposed in the oral cavity 4, the light absorption generated in the process until the near-infrared light L reaches the brain 5 is absorbed. It can be kept small. Thereby, even if the small light source 6 is used, near-infrared light L having an appropriate intensity is detected in the light receiver array 3.
また光源６は、光ファイバ８のみを口腔４内や鼻腔１２内に配置し、発生部７については口腔４や鼻腔１２の外側に配置してもよい。このようにしても、近赤外光Ｌを口腔４や鼻腔１２から脳５に向けて照射することができるとともに、発生部７として大型の機器を使用することができるために、より確実に適当な強度の近赤外光を受光器アレイ３に検出させることができる。 Moreover, the light source 6 may arrange | position only the optical fiber 8 in the oral cavity 4 or the nasal cavity 12, and may arrange | position the generation | occurrence | production part 7 in the oral cavity 4 or the nasal cavity 12 outside. Even if it does in this way, while being able to irradiate the near-infrared light L toward the brain 5 from the oral cavity 4 or the nasal cavity 12, since a large sized apparatus can be used as the generation | occurrence | production part 7, it is more appropriate. The near-infrared light having a high intensity can be detected by the light receiver array 3.
また、脳５の活動が神経細胞の電気活動により生じることに基づき、脳５の活動を検出する電磁波としてテラヘルツ波が使用されてもよい。このテラヘルツ波は、微弱電流に吸収される特性を有することから、集積回路の電気的な欠陥部位を調べるために使用されるが、神経細胞の電気活動においてもテラヘルツ波を吸収し得る電流が発生することから、神経細胞の電気活動を検出する電磁波としてテラヘルツ波は好適である。 Further, a terahertz wave may be used as an electromagnetic wave for detecting the activity of the brain 5 based on the activity of the brain 5 caused by the electrical activity of nerve cells. This terahertz wave has the property of being absorbed by a weak current, so it is used to investigate the electrical defect part of an integrated circuit. However, a current that can absorb the terahertz wave is also generated in the electrical activity of a nerve cell. Therefore, terahertz waves are suitable as electromagnetic waves for detecting the electrical activity of nerve cells.
以下、図１，２を再び用いて、テラヘルツ波による検出を行う脳機能計測装置の構成を説明する。なお、この構成を示す符号は括弧内に表記する。 Hereinafter, the configuration of a brain function measuring apparatus that performs detection using terahertz waves will be described with reference to FIGS. In addition, the code | symbol which shows this structure is described in a parenthesis.
図１に示すように、テラヘルツ波Ｔによる検出を行う脳機能計測装置３０は、頭皮２上に設けられる複数の検出器３１と、検出器３１と脳５を介して反対側に設けられる、一つのテラヘルツ波発生装置３２とから構成される。 As shown in FIG. 1, a brain function measuring device 30 that performs detection using a terahertz wave T includes a plurality of detectors 31 provided on the scalp 2 and provided on the opposite side via the detectors 31 and the brain 5. And two terahertz wave generators 32.
各検出器３１は頭皮２上の異なる位置に配置され、テラヘルツ波発生装置３２は、口腔４内に配置されることで前記検出器３１の反対側に設けられる。 Each detector 31 is arranged at a different position on the scalp 2, and the terahertz wave generation device 32 is provided in the opposite side of the detector 31 by being arranged in the oral cavity 4.
テラヘルツ波発生装置３２は、図２に示すように、テラヘルツ波Ｔを発生させる発生部３３と、発生部３３で発生したテラヘルツ波Ｔの出射方向を調整する光ファイバ３４とによって構成される。光ファイバ３４は、テラヘルツ波Ｔが脳５に向けて出射されるように、出射部３５の向きが調整される。また、光ファイバ３４の出射部３５には、テラヘルツ波Ｔを放射状に拡散する球面状のレンズ３６が取り付けられる。 As shown in FIG. 2, the terahertz wave generation device 32 includes a generation unit 33 that generates a terahertz wave T and an optical fiber 34 that adjusts the emission direction of the terahertz wave T generated by the generation unit 33. In the optical fiber 34, the direction of the emitting portion 35 is adjusted so that the terahertz wave T is emitted toward the brain 5. Further, a spherical lens 36 that diffuses the terahertz wave T radially is attached to the emitting portion 35 of the optical fiber 34.
以上の構成を有する脳機能計測装置３０では、口腔４内に配置されたテラヘルツ波発生装置３２から、脳５に向けてテラヘルツ波Ｔが出射されることで、テラヘルツ波Ｔは、脳５内を上方へ進行する。この際、テラヘルツ波発生装置３２から出射されたテラヘルツ波Ｔは、レンズ３６により放射状に拡散されることで、脳５の幅広い範囲を透過し、この過程で大脳皮質５０などの神経細胞を流れる電流に吸収される。そして、脳５を透過した各テラヘルツ波Ｔは、その進行方向の先に存在する検出器３１に検出されて、脳５の透過後における強度が計測される。そして、この計測された強度とテラヘルツ波発生装置３２からの出射時における強度との差から、テラヘルツ波Ｔの脳透過時における吸収量が得られ、この吸収量に基づき、脳５における神経細胞の電気活動が観測される。 In the brain function measuring device 30 having the above-described configuration, the terahertz wave T is emitted from the terahertz wave generating device 32 disposed in the oral cavity 4 toward the brain 5, so that the terahertz wave T passes through the brain 5. Proceed upward. At this time, the terahertz wave T emitted from the terahertz wave generating device 32 is diffused radially by the lens 36, thereby passing through a wide range of the brain 5, and in this process, a current flowing through nerve cells such as the cerebral cortex 50. To be absorbed. Then, each terahertz wave T transmitted through the brain 5 is detected by the detector 31 existing ahead in the traveling direction, and the intensity after transmission through the brain 5 is measured. Then, from the difference between the measured intensity and the intensity at the time of emission from the terahertz wave generation device 32, the amount of absorption of the terahertz wave T when transmitted through the brain is obtained. Electric activity is observed.
この脳機能計測装置３０によれば、検出器３１が頭皮上に設けられ、テラヘルツ波発生装置３２が、検出器３１と脳５を介して反対側に設けられることで、検出器３１では、脳５を直線的に透過したテラヘルツ波Ｔが受光される。このため、検出器３１に受光されるテラヘルツ波Ｔの経路が確定されるため、脳５の活動部位を特定することができる。 According to this brain function measuring device 30, the detector 31 is provided on the scalp, and the terahertz wave generating device 32 is provided on the opposite side via the detector 31 and the brain 5. The terahertz wave T linearly transmitted through 5 is received. For this reason, since the path of the terahertz wave T received by the detector 31 is determined, the active site of the brain 5 can be specified.
また、頭皮２上にテラヘルツ波発生装置３２を設けないようにしたことで、検出器３１をテラヘルツ波発生装置３２による制限なく頭皮２上に配置することができる。これにより、検出器３１を高密度に配置することができるため、高い空間分解能を得ることができる。 Further, since the terahertz wave generating device 32 is not provided on the scalp 2, the detector 31 can be disposed on the scalp 2 without restriction by the terahertz wave generating device 32. Thereby, since the detectors 31 can be arranged with high density, high spatial resolution can be obtained.
また、脳機能計測装置３０によれば、近赤外光Ｌを用いる脳機能計測装置１に比して、より直接的に脳５の活動を捉えることができる。すなわち、近赤外光Ｌによる検出は、血流におけるヘモグロビンの酸素化状態の変化を検出するものであるが、ヘモグロビン酸素化状態の変化は神経細胞の電気活動の数秒後に生じるものであるとともに、その変化が生じる位置は、電気活動を生じた神経細胞の位置とは必ずしも一致しない。このため、近赤外光Ｌによる検出では、その検出時間及び検出位置が、神経細胞の電気活動の発生時間及び発生位置からずれる虞れがある。これに対して、上述のテラヘルツ波Ｔを用いる脳機能計測装置３０によれば、神経細胞の電気活動を直接的に捉えることから、該神経細胞の電気活動が発生した時間や位置を正確に把握することができる。 Moreover, according to the brain function measuring device 30, the activity of the brain 5 can be captured more directly as compared with the brain function measuring device 1 using the near infrared light L. That is, the detection by the near-infrared light L detects a change in the oxygenated state of hemoglobin in the bloodstream, but the change in the hemoglobin oxygenated state occurs after a few seconds after the electrical activity of the nerve cell, The position where the change occurs does not necessarily coincide with the position of the nerve cell that caused the electrical activity. For this reason, in the detection by the near-infrared light L, the detection time and detection position may deviate from the generation time and generation position of the electrical activity of the nerve cell. On the other hand, according to the brain function measuring apparatus 30 using the above-described terahertz wave T, the electrical activity of the nerve cell is directly captured, so that the time and position where the electrical activity of the nerve cell is generated can be accurately grasped. can do.
また、テラヘルツ波発生装置３２にテラヘルツ波Ｔをミリ秒間隔で放出させることにより、神経細胞の電気活動をミリ秒オーダーで検出できる。これにより、高い時間分解能が得られる。 Further, by causing the terahertz wave generator 32 to emit the terahertz waves T at intervals of milliseconds, it is possible to detect the electrical activity of the nerve cell in the order of milliseconds. Thereby, high time resolution is obtained.
なお、テラヘルツ波発生装置３２を脳５により近接した位置に設けるべく、テラヘルツ波発生装置３２は、鼻腔１２内に配置され得る。 Note that the terahertz wave generation device 32 may be disposed in the nasal cavity 12 in order to provide the terahertz wave generation device 32 at a position closer to the brain 5.
１，３０ 脳機能計測装置
２ 頭皮
３ 受光器アレイ
４ 口腔
５ 脳
６ 光源
７，３３ 発生部
８，３４ 光ファイバ
９，３５ 出射部
１０，３６ レンズ
１２ 鼻腔
３１ 検出器
３２ テラヘルツ波発生装置
５０ 大脳皮質
DESCRIPTION OF SYMBOLS 1,30 Brain function measuring apparatus 2 Scalp 3 Light receiver array 4 Oral cavity 5 Brain 6 Light source 7,33 Generation | occurrence | production part 8,34 Optical fiber 9,35 Emitting part 10,36 Lens 12 Nasal cavity 31 Detector 32 Terahertz wave generator 50 Cerebrum cortex
Claims (9)
脳を透過した前記電磁波を検出する電磁波検出手段とを備え、
前記電磁波検出手段は、頭皮上に設けられ、
前記電磁波発生手段は、前記電磁波検出手段と脳を介して反対側に設けられることを特徴とする脳機能計測装置。 Electromagnetic wave generating means for emitting electromagnetic waves toward the brain;
An electromagnetic wave detecting means for detecting the electromagnetic wave transmitted through the brain,
The electromagnetic wave detection means is provided on the scalp,
The apparatus for measuring brain function, wherein the electromagnetic wave generating means is provided on the opposite side of the electromagnetic wave detecting means via the brain.
前記電磁波検出手段は、脳を透過した前記近赤外光を受光する受光器アレイであることを特徴とする請求項１に記載の脳機能計測装置。 The electromagnetic wave generating means is a light source that emits near-infrared light as the electromagnetic wave toward the brain,
2. The brain function measuring apparatus according to claim 1, wherein the electromagnetic wave detecting means is a light receiver array that receives the near infrared light transmitted through the brain.
前記電磁波検出手段は、脳を透過した前記テラヘルツ波を検出する検出器であることを特徴とする請求項１に記載の脳機能計測装置。 The electromagnetic wave generating means is a terahertz wave generator that emits a terahertz wave as the electromagnetic wave toward the brain,
The brain function measuring apparatus according to claim 1, wherein the electromagnetic wave detecting means is a detector that detects the terahertz wave transmitted through the brain.
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