JP2020183898A - Sound wave detection device - Google Patents
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- Measurement Of Mechanical Vibrations Or Ultrasonic Waves (AREA)
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
Abstract
Description
本発明は、音波検出装置に関する。 The present invention relates to a sound wave detection device.
生体情報を音として取得する機器として、従来から聴診器、加速度メーター等が用いられており、心臓のモニタリングには心電計が用いられている。しかし、これらの装置では、生態情報を高い精度で取得することが困難な場合があった。特に、心音から疾病を検出する際には、複数の周波数領域の心拍音の差異を検出することが重要であるが、上記従来の機器、装置では、検出感度が不足していた。また、長期間継続して生体情報の取得を行う場合には、電源の確保のために大がかりな装置になるという問題もあった。 A stethoscope, an accelerometer, or the like has been conventionally used as a device for acquiring biological information as sound, and an electrocardiograph is used for monitoring the heart. However, with these devices, it was sometimes difficult to acquire ecological information with high accuracy. In particular, when detecting a disease from heart sounds, it is important to detect differences in heartbeat sounds in a plurality of frequency regions, but the above-mentioned conventional devices and devices have insufficient detection sensitivity. In addition, when the biological information is continuously acquired for a long period of time, there is a problem that it becomes a large-scale device for securing a power source.
そこで、下記非特許文献１には、ピエゾ素子とトライボエレクトリック素子との混成素子による、電源不要で生体情報の取得にも適用できる装置が開示されている。 Therefore, Non-Patent Document 1 below discloses a device using a hybrid element of a piezo element and a triboelectric element, which does not require a power source and can be applied to the acquisition of biological information.
しかし、上記非特許文献１の技術では、アーチ上に形成されたピエゾ素子に外力を作用させる必要があるので、エネルギーが微少である低周波数域の心音等の生体情報を高感度で検出することが困難であるという問題がある。 However, in the technique of Non-Patent Document 1, it is necessary to apply an external force to the piezo element formed on the arch, so that biological information such as heart sounds in a low frequency region where energy is minute is detected with high sensitivity. There is a problem that it is difficult.
本発明の目的は、生体情報を音として高感度で取得することができる音波検出装置を提供することにある。 An object of the present invention is to provide a sound wave detection device capable of acquiring biological information as sound with high sensitivity.
上記目的を達成するために、本発明の一実施形態は、音波検出装置であって、導電性繊維で構成された第１繊維層と、複数の前記第１繊維層の間に挿入され、非導電性繊維で構成された第２繊維層と、を備えることを特徴とする。 In order to achieve the above object, one embodiment of the present invention is a sound wave detection device, which is inserted between a first fiber layer composed of conductive fibers and a plurality of the first fiber layers, and is not. It is characterized by including a second fiber layer made of conductive fibers.
上記第１繊維層を構成する導電性繊維は、導電性物質が樹脂繊維表面にコーティングされた繊維であるのが好適である。 The conductive fiber constituting the first fiber layer is preferably a fiber in which a conductive substance is coated on the surface of the resin fiber.
また、上記導電性物質は金であるのが好適である。 Further, the conductive substance is preferably gold.
また、上記第２繊維層を構成する非導電性繊維が、ポリフッ化ビニリデンの繊維であるのが好適である。 Further, it is preferable that the non-conductive fiber constituting the second fiber layer is a polyvinylidene fluoride fiber.
本発明によれば、生体情報を音として高感度で取得することができる。 According to the present invention, biological information can be acquired as sound with high sensitivity.
以下、本発明を実施するための形態（以下、実施形態という）を、図面に従って説明する。 Hereinafter, embodiments for carrying out the present invention (hereinafter referred to as embodiments) will be described with reference to the drawings.
図１には、実施形態に係る音波検出装置の構成例が示される。図１において、音波検出装置は、導電性繊維で構成された複数の第１繊維層１０と、上記第１繊維層の間に挿入され、非導電性繊維で構成された第２繊維層１２とを有する。なお、図１では、２層の第１繊維層１０の間に第２繊維層１２が挿入された例が示されているが、これには限定されず、複数の第１繊維層１０のそれぞれの間（例えば、第１繊維層が５層であれば、それぞれの間は４つある）に第２繊維層１２が挿入された構造であればよい。また、上記第１繊維層１０には、出力を取り出すための出力電極１４が接続されている。 FIG. 1 shows a configuration example of the sound wave detection device according to the embodiment. In FIG. 1, the sound wave detection device includes a plurality of first fiber layers 10 made of conductive fibers and a second fiber layer 12 inserted between the first fiber layers and made of non-conductive fibers. Has. Note that FIG. 1 shows an example in which the second fiber layer 12 is inserted between the first fiber layers 10 of the two layers, but the present invention is not limited to this, and each of the plurality of first fiber layers 10 is not limited to this. The structure may be such that the second fiber layer 12 is inserted between the spaces (for example, if the first fiber layer is five layers, there are four between each). Further, an output electrode 14 for taking out an output is connected to the first fiber layer 10.
図１に示された例では、第１繊維層１０が窓枠２０に支持されており、第２繊維層１２とともに積層されている。なお、図１では、第１繊維層１０と第２繊維層１２との間の空隙の距離が長く記載されているが、これは説明の便宜のためであって、各層間の距離が１〜１００μｍ程度になるように近接して配置される。 In the example shown in FIG. 1, the first fiber layer 10 is supported by the window frame 20 and is laminated together with the second fiber layer 12. In FIG. 1, the distance between the first fiber layer 10 and the second fiber layer 12 is shown to be long, but this is for convenience of explanation, and the distance between the layers is 1 to 1. They are arranged close to each other so as to be about 100 μm.
図２には、第１繊維層１０及び第２繊維層１２の詳細構成例が示される。図２において、第１繊維層１０は、ポリウレタン（ＰＵ）繊維の表面がパリレン（パラキシリレン系樹脂 登録商標）でコーティングされ、さらにパリレンのコーティング層の上に金（Ａｕ）がコーティングされた導電性繊維で構成されている。ＰＵ繊維（ＰＵナノファイバー）は、例えばエレクトロスピニングにより得ることができる。また、パリレンのコーティングは、化学気相法（ＣＶＤ法）により真空チャンバー中で形成することができ、金のコーティングは、真空チャンバーを用いた加熱蒸着により形成することができる。 FIG. 2 shows a detailed configuration example of the first fiber layer 10 and the second fiber layer 12. In FIG. 2, the first fiber layer 10 is a conductive fiber in which the surface of a polyurethane (PU) fiber is coated with parylene (a registered trademark of a paraxylylene resin), and gold (Au) is further coated on the parylene coating layer. It is composed of. PU fibers (PU nanofibers) can be obtained, for example, by electrospinning. Further, the parylene coating can be formed in a vacuum chamber by a chemical vapor deposition method (CVD method), and the gold coating can be formed by heat vapor deposition using a vacuum chamber.
図２の例では、第１繊維層１０が、窓枠２０に支持されており、窓枠２０を用いて第２繊維層１２を挟持し、この状態で第１繊維層１０と第２繊維層１２とが積層されている。 In the example of FIG. 2, the first fiber layer 10 is supported by the window frame 20, the second fiber layer 12 is sandwiched by the window frame 20, and the first fiber layer 10 and the second fiber layer are in this state. 12 and 12 are laminated.
上記金のコーティングは、矩形状のポリウレタン繊維層（第１繊維層１０）の周囲の窓枠２０に支持された部分を除いた領域に形成されてもよいし、ポリウレタン繊維層の全体領域に形成してもよい。以後、金をコーティングした領域を電極領域１８という。なお、上記ポリウレタン繊維層に電極領域１８を形成する場合には、図１に示した出力電極１４と接続するための出力取出領域１６にも金をコーティングし、出力取出領域１６と電極領域１８とを電気的に接続する。 The gold coating may be formed in a region excluding a portion supported by the window frame 20 around the rectangular polyurethane fiber layer (first fiber layer 10), or may be formed in the entire region of the polyurethane fiber layer. You may. Hereinafter, the gold-coated region is referred to as an electrode region 18. When the electrode region 18 is formed on the polyurethane fiber layer, the output take-out region 16 for connecting to the output electrode 14 shown in FIG. 1 is also coated with gold to form the output take-out region 16 and the electrode region 18. Electrically connect.
また、第２繊維層１２は、上述の通り非導電性繊維で構成されている。この非導電性繊維としては、圧電材料であるポリフッ化ビニリデン（ＰＶＤＦ）の繊維を使用するのが好適である。ポリフッ化ビニリデンの繊維を使用することにより、第２繊維層１２が音波により振動する際に、トライボエレクトリック効果に加え、圧電効果も得ることができるので、出力として取り出せる波形からより多くの生体情報を得ることができる。 Further, the second fiber layer 12 is composed of non-conductive fibers as described above. As the non-conductive fiber, it is preferable to use a fiber of polyvinylidene fluoride (PVDF) which is a piezoelectric material. By using polyvinylidene fluoride fibers, when the second fiber layer 12 vibrates due to sound waves, in addition to the triboelectric effect, a piezoelectric effect can also be obtained, so more biological information can be obtained from the waveform that can be extracted as an output. Obtainable.
上記ＰＶＤＦとしては、結晶構造がβ相であるのが、他の結晶構造（α相、γ相）より双極子モーメントが高く、高い圧電効果を示すため、好適である。この場合、結晶構造が完全にβ相のみの材料でなくてもβ相の割合が多ければ、高い圧電効果を示すことができる。 As the PVDF, it is preferable that the crystal structure is β phase because the dipole moment is higher than other crystal structures (α phase, γ phase) and a high piezoelectric effect is exhibited. In this case, even if the crystal structure is not a material having only β phase, a high piezoelectric effect can be exhibited if the ratio of β phase is large.
第２繊維層１２を構成するＰＶＤＦ等の非導電性繊維には、例えばエレクトロスピニングにより得たＰＶＤＦナノファイバーを使用することができる。 For non-conductive fibers such as PVDF constituting the second fiber layer 12, for example, PVDF nanofibers obtained by electrospinning can be used.
図３には、以上のようにして構成した音波検出装置の平面図が示される。図３は、外部から第１繊維層１０を見た図である。図３に示されるように、２枚ある第１繊維層１０のそれぞれには、電極領域１８と出力取出領域１６とが設けられている。また、第１繊維層１０は、窓枠２０に支持されている。電極領域１８と出力取出領域１６とは、上述したように金の蒸着により構成されている。 FIG. 3 shows a plan view of the sound wave detection device configured as described above. FIG. 3 is a view of the first fiber layer 10 viewed from the outside. As shown in FIG. 3, each of the two first fiber layers 10 is provided with an electrode region 18 and an output extraction region 16. Further, the first fiber layer 10 is supported by the window frame 20. The electrode region 18 and the output extraction region 16 are formed by vapor deposition of gold as described above.
図４には、実施形態にかかる音波検出装置の動作の説明図が示される。図４において、音波Ａが音波検出装置の一方の第１繊維層１０に到達すると（Ｉ）、第１繊維層１０の繊維の間隙を通過して、第１繊維層１０の間に挿入された第２繊維層１２を振動させる。 FIG. 4 shows an explanatory diagram of the operation of the sound wave detection device according to the embodiment. In FIG. 4, when the sound wave A reaches one of the first fiber layers 10 of the sound wave detection device (I), it passes through the gaps between the fibers of the first fiber layer 10 and is inserted between the first fiber layers 10. The second fiber layer 12 is vibrated.
図４の例では、音波Ａにより生じた空気の振動に応じて、第２繊維層１２が図の右方向に凸になるように変形し、第２繊維層１２が図の右側の第１繊維層１０の電極領域１８（図示せず）に接触する（ＩＩ）。次に、第２繊維層１２の右方向に凸の変形が無くなり第２繊維層１２と第１繊維層１０との接触が無くなる（ＩＩＩ）。さらに、上記空気の振動に応じて、第２繊維層１２が図の左方向に凸になるように変形し、第２繊維層１２が図の左側の第１繊維層１０の電極領域１８（図示せず）に接触する（ＩＶ）。 In the example of FIG. 4, the second fiber layer 12 is deformed so as to be convex to the right in the figure in response to the vibration of the air generated by the sound wave A, and the second fiber layer 12 is the first fiber on the right side of the figure. Contact the electrode region 18 (not shown) of layer 10 (II). Next, the convex deformation of the second fiber layer 12 in the right direction disappears, and the contact between the second fiber layer 12 and the first fiber layer 10 disappears (III). Further, in response to the vibration of the air, the second fiber layer 12 is deformed so as to be convex to the left in the figure, and the second fiber layer 12 is the electrode region 18 of the first fiber layer 10 on the left side in the figure (FIG. Not shown) (IV).
以上の動作を繰り返し、第１繊維層１０の電極領域１８と第２繊維層１２との接触、非接触に基づいてトライボエレクトリック効果が発現し、第２繊維層１２の変形により第２繊維層１２を構成するＰＶＤＦ繊維に圧電効果が発現する。この際に発現したトライボエレクトリック効果及び圧電効果は、電極領域１８と電気的に接続された出力取出領域１６及び出力電極１４を介して出力信号として取り出すことができる。この結果、音波検出装置に到達した音波Ａから、様々な生体情報を得ることができる。 By repeating the above operation, the triboelectric effect is exhibited based on the contact and non-contact between the electrode region 18 of the first fiber layer 10 and the second fiber layer 12, and the second fiber layer 12 is deformed by the deformation of the second fiber layer 12. A piezoelectric effect is exhibited in the PVDF fibers constituting the above. The triboelectric effect and the piezoelectric effect exhibited at this time can be taken out as an output signal via the output extraction region 16 and the output electrode 14 electrically connected to the electrode region 18. As a result, various biological information can be obtained from the sound wave A that has reached the sound wave detection device.
以下、本発明の実施例を具体的に説明する。なお、以下の実施例は、本発明の理解を容易にするためのものであり、本発明はこれらの実施例に制限されるものではない。 Hereinafter, examples of the present invention will be specifically described. The following examples are for facilitating the understanding of the present invention, and the present invention is not limited to these examples.
実施例１＜ポリウレタンナノファイバー基板（第１繊維層）の作製＞
ポリウレタンナノファイバーシートを、”Miyamoto et al. Nature Nanotechnology、P.907-913, Vol.12, 2017”の記載に基づき、下記の通り適宜変更して作製した。
Example 1 <Preparation of polyurethane nanofiber substrate (first fiber layer)>
A polyurethane nanofiber sheet was prepared by appropriately modifying it as follows based on the description of "Miyamoto et al. Nature Nanotechnology, P.907-913, Vol.12, 2017".
ポリウレタン溶液（大日精化製、Ｒｅｚａｍｉｎ Ｍ−８１１５ＬＰ）をＤＭＦ（Ｎ，Ｎ−ジメチルホルムアミド）とＭＥＫ（メチルエチルケトン）との混合溶媒（富士フイルム和光純薬株式会社製 質量比ＤＭＦ：ＭＥＫ＝７：３）により希釈して１５％溶液を作製し、室温下２時間マグネティックスターラーを用いて攪拌した。 Polyurethane solution (manufactured by Dainichi Seika, Rezamin M-8115LP) mixed solvent of DMF (N, N-dimethylformamide) and MEK (methylethylketone) (manufactured by Fujifilm Wako Pure Chemical Industries, Ltd. Mass ratio DMF: MEK = 7: 3) ) To prepare a 15% solution, which was stirred at room temperature for 2 hours using a magnetic stirrer.
当該ポリウレタン溶液を用いてエレクトロスピニング装置（Ｆｕｅｎｃｅ ｅｓ−２０００）により以下の手順でポリウレタンナノファイバーシートを作製した。すなわち、２７Ｇ（ゲージ）の金属針を装着したガラスシリンジにポリウレタン溶液を注入し、射出距離（金属針先端と後述するポリイミドフィルムとの間の距離）１５ｃｍ、射出速度１０μＬ／分、印加電圧２０ｋＶの射出条件で、フッ素樹脂を表面に犠牲層としてコーティングしたポリイミドフィルム上に５分間ポリウレタンナノファイバーを射出しポリウレタンナノファイバーシートを作製した。射出したポリウレタンナノファイバーの径は５００ｎｍであった。 Using the polyurethane solution, a polyurethane nanofiber sheet was prepared by an electrospinning device (Fuence es-2000) according to the following procedure. That is, the polyurethane solution is injected into a glass syringe equipped with a 27 G (gauge) metal needle, and the injection distance (distance between the tip of the metal needle and the polyimide film described later) is 15 cm, the injection speed is 10 μL / min, and the applied voltage is 20 kV. Under the injection conditions, polyurethane nanofibers were injected for 5 minutes onto a polyimide film coated with a fluororesin as a sacrificial layer to prepare a polyurethane nanofiber sheet. The diameter of the injected polyurethane nanofibers was 500 nm.
作製したポリウレタンナノファイバーシートは、内側のサイズが２．５×２．５ｃｍの窓枠上に転写した。この窓枠は、パリレン支持層を１μｍの厚みに蒸着した１２５μｍ厚みのポリイミドである。パリレン支持層は、厚さ１２５μｍのポリイミドフィルム（東レ・デュポン株式会社製 上記サイズの枠状に形成）上に、日本パリレン社製のラボコータＰＤＳ−２０１０を用いて化学気相成長法（ＣＶＤ）でパリレン（ＫＩＳＣＯ社製 ｄｉｘ−ＳＲ）を蒸着し、作製したものである。 The produced polyurethane nanofiber sheet was transferred onto a window frame having an inner size of 2.5 × 2.5 cm. This window frame is a 125 μm-thick polyimide in which a parylene support layer is vapor-deposited to a thickness of 1 μm. The parylene support layer is formed by a chemical vapor deposition (CVD) method using a lab coater PDS-2010 manufactured by Japan Parylene Co., Ltd. on a polyimide film having a thickness of 125 μm (formed in a frame shape of the above size manufactured by Toray DuPont Co., Ltd.). It was produced by vapor-depositing parylene (dix-SR manufactured by KISCO).
上記ポリウレタンナノファイバーを射出したポリイミドフィルムはポリウレタンナノファイバー基板を製造する際の一時的な基板として用い、表面には犠牲層としてフッ素樹脂を、ミカサ株式会社製ＭＳ−Ｂ１００を使用してスピンコートで形成した。次いでポリウレタンナノファイバーシートを上記窓枠のパリレン支持層上に転写した。ここで、転写とは、フッ素樹種をコーティングしたポリイミドフィルムからポリウレタンナノファイバーシートを剥離させ、窓枠のパリレン支持層上に載せて固定することをいう。 The polyimide film on which the polyurethane nanofibers are injected is used as a temporary substrate when manufacturing a polyurethane nanofiber substrate, and fluororesin is used as a sacrificial layer on the surface, and MS-B100 manufactured by Mikasa Co., Ltd. is used for spin coating. Formed. The polyurethane nanofiber sheet was then transferred onto the parylene support layer of the window frame. Here, transfer means peeling a polyurethane nanofiber sheet from a polyimide film coated with a fluorine tree species, placing it on a parylene support layer of a window frame, and fixing it.
以上の製法により、ポリウレタンナノファイバーシートは、窓枠の上ではポリイミド支持層上に支持され、窓枠の内側では自立している（固定されていない）構成になっている。 According to the above manufacturing method, the polyurethane nanofiber sheet is supported on the polyimide support layer on the window frame, and is self-supporting (not fixed) inside the window frame.
次いで、厚さ２００ｎｍのパリレン層を、ポリウレタンナノファイバーシートの各ポリウレタンナノファイバーの表面にコーティングし、ファイバー同士の接合を補強した。その後、各ポリウレタンナノファイバーの表面にコーティングされたパリレン層の上に、真空チャンバー（ＵＬＶＡＣ社製ＥＸ−２００）を用いた加熱蒸着により、シャドウマスクを用いて８０〜１００ｎｍ厚さの金を蒸着させ、図２に示された出力取出領域１６と電極領域１８とを形成することでポリウレタンナノファイバー基板を製造した。なお、ポリウレタンナノファイバー基板の厚さはエレクトロスピニングの射出時間により調整することができる。 Next, a 200 nm-thick parylene layer was coated on the surface of each polyurethane nanofiber of the polyurethane nanofiber sheet to reinforce the bonding between the fibers. Then, on the parylene layer coated on the surface of each polyurethane nanofiber, gold having a thickness of 80 to 100 nm is vapor-deposited using a shadow mask by thermal vapor deposition using a vacuum chamber (EX-200 manufactured by ULVAC). , The polyurethane nanofiber substrate was manufactured by forming the output extraction region 16 and the electrode region 18 shown in FIG. The thickness of the polyurethane nanofiber substrate can be adjusted by the injection time of electrospinning.
実施例２＜ＰＶＤＦ（ポリフッ化ビニリデン）ナノファイバーシート（第２繊維層）の作製＞
ＰＶＤＦナノファイバーシートも、上記実施例１と同様にエレクトロスピニング装置（Ｆｕｅｎｃｅ ＥＳ−２０００）を用いて作製した。
Example 2 <Preparation of PVDF (polyvinylidene fluoride) nanofiber sheet (second fiber layer)>
The PVDF nanofiber sheet was also produced by using an electrospinning device (Fuence ES-2000) in the same manner as in Example 1 above.
まず、２ｇのＰＶＤＦペレット（モル質量２７５，０００ｇｍｏｌ−１，シグマアルドリッチ社製）を、容量比４：６で混合したＤＭＦとアセトンとの混合溶媒中に溶解した。その後２時間７０℃で攪拌し、続けて室温で一晩攪拌して１９質量％のＰＶＤＦ溶液を調整した。このＰＶＤＦ溶液を、金属針（２７ゲージ）を装着したガラスシリンジに注入し、シリコンコーティングをした紙の上にＰＶＤＦナノファイバーを射出しＰＶＤＦナノファイバーシート（３．５×４．５ｃｍ）を作製した。 First, 2 g of PVDF pellets (molar mass 275,000 gmol -1 , manufactured by Sigma-Aldrich) were dissolved in a mixed solvent of DMF and acetone mixed at a volume ratio of 4: 6. Then, the mixture was stirred at 70 ° C. for 2 hours and then overnight at room temperature to prepare a 19 mass% PVDF solution. This PVDF solution was injected into a glass syringe equipped with a metal needle (27 gauge), and PVDF nanofibers were injected onto silicon-coated paper to prepare a PVDF nanofiber sheet (3.5 x 4.5 cm). ..
この場合、射出条件である射出距離は１５ｃｍに維持し、ＰＶＤＦナノファイバーシート形成のため２０分間ＰＶＤＦナノファイバーを射出した。このとき、エレクトロスピニングの条件設定のため３つのパラメータ（溶液濃度、印加電圧、射出速度）について検証した。具体的には、溶液濃度１５−２３％、印加電圧１５−３０ｋＶ、射出速度５−１５μＬ／分の範囲で検証し、ＰＶＤＦナノファイバー形成の最適条件を検討した。その検証結果から、エレクトロスピニングの最適条件を、溶液濃度１９質量％、印加電圧２０ｋＶ及び射出速度１０μＬ／分と設定した。 In this case, the injection distance, which is an injection condition, was maintained at 15 cm, and PVDF nanofibers were injected for 20 minutes to form a PVDF nanofiber sheet. At this time, three parameters (solution concentration, applied voltage, and injection speed) were verified for setting the conditions for electrospinning. Specifically, the solution concentration was 15-23%, the applied voltage was 15-30 kV, and the injection speed was 5-15 μL / min, and the optimum conditions for PVDF nanofiber formation were examined. From the verification results, the optimum conditions for electrospinning were set to a solution concentration of 19% by mass, an applied voltage of 20 kV, and an injection speed of 10 μL / min.
実施例３＜ナノファイバー及び音波検出装置の特性試験＞
・ナノファイバー特性測定
実施例１及び実施例２で製造したポリウレタン及びＰＶＤＦのナノファイバーそれぞれについて、その構造を走査型電子顕微鏡（Ｈｉｔａｃｈｉ Ｓ−４８００，ＦＥ−ＳＥＭ）（以下、ＳＥＭ）で検証した。ＳＥＭ画像を撮影し、画像処理ソフト（ＩｍａｇｅＪ）を用いてナノファイバーの直径を算出した。ポリウレタンナノファイバーの直径は５００ｎｍ，ＰＶＤＦナノファイバーの直径は４００ｎｍであった。
Example 3 <Characteristic test of nanofiber and sound wave detection device>
-Measurement of nanofiber characteristics The structures of the polyurethane and PVDF nanofibers produced in Example 1 and Example 2 were verified with a scanning electron microscope (Hitachi S-4800, FE-SEM) (hereinafter, SEM). An SEM image was taken and the diameter of the nanofiber was calculated using image processing software (ImageJ). The diameter of the polyurethane nanofibers was 500 nm, and the diameter of the PVDF nanofibers was 400 nm.
次に、Ｃｕ−Ｋα線（λ＝１．５４１Å（０．１５４１ｎｍ））を使用し、４０ｋＶ、３０ｍＡの条件でＸ線回折装置（リガク社製 ＳｍａｒｔＬａｂ）によりアウトオブプレーン（Ｏｕｔ ｏｆ ｐｌａｎｅ）法のＸ線回折を行い、ＰＶＤＦナノファイバーの結晶構造がβ相であることを確認した。試料は、スキャンレート０．２°／秒、測定ステップを０．０２°とし、２θ−θ構成として１０°から６０°までを測定した。Ｘ線測定中、試料はガラス製のホルダに載置された。 Next, using Cu-Kα rays (λ = 1.541 Å (0.1541 nm)), an out-of-plane method was performed using an X-ray diffractometer (SmartLab manufactured by Rigaku Corporation) under the conditions of 40 kV and 30 mA. X-ray diffraction was performed to confirm that the crystal structure of the PVDF nanofiber was β phase. The sample was measured at a scan rate of 0.2 ° / sec, a measurement step of 0.02 °, and a 2θ−θ configuration from 10 ° to 60 °. During the X-ray measurement, the sample was placed in a glass holder.
・音波検出装置の作製
実施例２で製造したＰＶＤＦナノファイバーシート（第２繊維層）を実施例１で製造したポリウレタンナノファイバー基板（第１繊維層）の間に挿入し、上記窓枠を用いて挟持し、この構造を３層積層して音波検出装置を形成した。
-Manufacture of sound wave detection device The PVDF nanofiber sheet (second fiber layer) manufactured in Example 2 is inserted between the polyurethane nanofiber substrates (first fiber layer) manufactured in Example 1, and the above window frame is used. This structure was laminated in three layers to form a sound wave detection device.
・音波検出装置のアコースティック特性の測定
アコースティック特性の測定は、拡声器をパーソナルコンピュータ（ＰＣ）に接続し、音源として用いた。音の周波数及び音圧レベルは、オーディオテストソフトを用いて周波数１０Ｈｚ〜１０，０００Ｈｚ、音圧９８ｄＢで制御した。なお、音圧レベルは、音圧レベル測定器を用いて測定した。音波検出装置からの電気的出力信号は、音波検出装置の出力取出領域１６に接続した出力電極１４を介し、オシロスコープに入力して測定した。測定試験中、測定機器から生じる偽振動を避けるため、重量のある石板で支持された固定枠に音波検出装置を取り付けた。
-Measurement of acoustic characteristics of sound wave detector For measurement of acoustic characteristics, a loudspeaker was connected to a personal computer (PC) and used as a sound source. The sound frequency and sound pressure level were controlled at a frequency of 10 Hz to 10,000 Hz and a sound pressure of 98 dB using audio test software. The sound pressure level was measured using a sound pressure level measuring device. The electrical output signal from the sound wave detection device was input to an oscilloscope and measured via the output electrode 14 connected to the output extraction area 16 of the sound wave detection device. During the measurement test, a sound wave detector was attached to a fixed frame supported by a heavy stone plate to avoid false vibrations generated by the measuring equipment.
図５には、音波検出装置のアコースティック特性の測定結果が示される。図５において、横軸が音の周波数であり、縦軸が音波検出装置からの出力電圧である。図５に示されるように、心音の測定領域である１０Ｈｚから２０００Ｈｚの範囲で高い出力電圧が得られた。これにより、実施例に係る音波検出装置は、心音測定に好適であることがわかる。 FIG. 5 shows the measurement results of the acoustic characteristics of the sound wave detection device. In FIG. 5, the horizontal axis is the frequency of sound, and the vertical axis is the output voltage from the sound wave detection device. As shown in FIG. 5, a high output voltage was obtained in the range of 10 Hz to 2000 Hz, which is the measurement region of heart sounds. From this, it can be seen that the sound wave detection device according to the embodiment is suitable for heart sound measurement.
実施例４＜心音測定＞
実施例３に係る音波検出装置を人の胸部上、僧帽弁の位置に取り付けて心音を測定した。心音信号の測定にはＮｅｕｒｏｐａｃｋ（日本光電社製 ＭＥＢ ９４０２）を用いた。
Example 4 <Heart sound measurement>
The sound wave detection device according to Example 3 was attached to the position of the mitral valve on the chest of a person to measure heart sounds. Neuropack (MEB 9402 manufactured by Nihon Kohden Co., Ltd.) was used for the measurement of the heart sound signal.
図６には、心音の測定結果が示される。図６において、横軸が音の測定時間であり、縦軸が音波検出装置からの出力電圧である。図６に示されるように、良好な心音波形を得ることができた。これにより、心音を高感度で取得できることがわかる。 FIG. 6 shows the measurement results of heart sounds. In FIG. 6, the horizontal axis is the sound measurement time, and the vertical axis is the output voltage from the sound wave detection device. As shown in FIG. 6, a good heart sound waveform could be obtained. From this, it can be seen that the heart sounds can be acquired with high sensitivity.
１０ 第１繊維層、１２ 第２繊維層、１４ 出力電極、１６ 出力取出領域、１８ 電極領域、２０ 窓枠。
10 1st fiber layer, 12 2nd fiber layer, 14 output electrodes, 16 output extraction areas, 18 electrode areas, 20 window frames.
Claims (4)
複数の前記第１繊維層の間に挿入され、非導電性繊維で構成された第２繊維層と、
を備える、音波検出装置。 The first fiber layer composed of conductive fibers and
A second fiber layer inserted between the plurality of first fiber layers and composed of non-conductive fibers,
A sound wave detection device.
The sound wave detection device according to any one of claims 1 to 3, wherein the non-conductive fiber constituting the second fiber layer is a fiber of polyvinylidene fluoride.
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