1294000 九、發明說明： 【發明所屬之技術領域】 本發明是有關於-種導電織物，特別是一種能摘測形 變之導電織物。 【先前技術】 谓測形變的織物商機廣大，可用來镇測外力的大小和 外力作用的頻率。因為镇測形變的織物為有彈性的織物， 所以’不同於其他的感測器’偵測形變的織物可以自由套 在物體上，量測物體體積變化的大小和變化的頻率。 習知偵測形變之織物是在彈性織物中織入光纖。當彈 性織物因外力造成形變，彈性織物内光纖的彎曲角度也會 隨之改變，因而影響到光在光纖内的傳遞。藉由偵測光的 訊號強弱的變化，得到外力作用的大小和頻率。 用光纖偵測的缺點在於光纖本身的成本高，偵測光的 訊號裝置過於複雜。並且’若織物有太大的形變時，會導 致光纖彎曲度過大，以致於光纖故障。 另一種偵測裝置，是在彈性織物中織入金屬線圈，對 金屬線圈通入電流，使金屬線圈感應形成磁場。將此彈性 織物套在有規律體積變化的物體上時，物體體積的變化會 對磁場的強度造成影響，藉由偵測磁場強度變化的頻率， 得到與物體體積變化有關的資訊。 用金屬線圈偵測的缺點在於易受外來磁場干擾其量測 的準確性。此外，無論是金屬線圈還是光纖，水洗後很容 1294000 易發生變形和變質。 【發明内容】 因此本發明的目的之一就是/在提供一種偵測形變之導 電織物，利用導電織物的電阻變化測得物體形變的大小和 頻率，偵測方式簡易，實用性高。 本發明的另一目的是在提供一種呼吸頻率偵測裝置， 此種偵測裝置藉由量測導電織物的電阻變化得到呼吸的頻 率，可用來預防嬰兒猝死，以及監測睡眠時是否有呼吸中 斷現象來監測睡眠的品質。 根據本發明之上述目的，提出一種偵測形變之導電織 物’包含至少一條包繞導電紗線，此包繞導電紗線由至少 一條導電纖維包繞於一條彈性紗線所構成，當此包繞導電 紗線受到外力產生形變時，這些導電纖維彼此之間會形成 多個接觸點，導電織物之電阻也會隨之改變。 根據本發明之上述目的，提出一種偵測形變之導電織 物’包含至少二條包繞導電紗線，每一包繞導電紗線由一 條導電纖維包繞於一條彈性紗線上所構成，當包繞導電紗 線受到外力產生形變時，相鄰之包繞導電紗線上之導電纖 維之間形成複數個接觸點，導電織物之電阻會隨之改變。 根據本發明之上述目的，提出一種呼吸頻率偵測裝 置包含上述之導電織物和彳貞測電路。上述之導電織物係 伏貼於一使用者身上，讓該使用者之呼吸可使上述之導電 織物產生形變而改變其電阻。而偵測電路用以偵測導電織 1294000 物電阻的變化頻率，以得到使用者之呼吸頻率。 —、由上述可知’本發明的偵測形變之導電織物，藉由導 電纖維的電阻變化測得物體形變的大小和頻率。配合簡易 靈敏度咼之偵測電路，可應用在例如監視呼吸頻率上。 因此y用本發明所提供之裝置來㈣嬰兒猝死以及監測睡 眠時疋否有呼吸中斷現象來監測睡眠的品質。 【實施方式】 本發明的摘測形變之導電織物主要包含包繞導電紗 ^ 〇‘電沙線的結構有兩種，一種為雙包繞，一種為 單匕、％如第1 a圖所示為雙包繞導電紗線，在不導電的彈 性紗線110外包繞至少兩條的導電纖維。以第一導電纖維 120和第一、電纖維13〇表示，第一導電纖維以〇和第二導 電纖維130交錯包繞於彈性紗線110夕卜。因為，第一導電 纖維120和第二導電纖維13()包繞的很鬆，所以，不僅第 導電纖維120和第二導電纖、維13()沒有緊貼彈性紗線 ιι〇ϋ電、_ 12()和第二導電纖維i3G彼此也沒有接 貧。在較佳的實施例中，導電纖維為碳黑纖維、銅離子纖 維或鍍娘纖維。導電纖維之比電阻較佳約A 1〇2〜106 Ohms/cm 〇 如第1B圖所示，當對此雙包繞導電紗線施力時，彈七 紗線110會因為受力而如且 ,,., 力而拉長。此外，原本鬆鬆的包繞在费 性紗線110上的第-導電纖維120和第二導電纖維13" 因為施力而與彈性紗線11G貼緊，以致於第—導電纖維^ 7 1294000 和苐'一導電纖維13 0之彼此接觸’在兩者之間形成多個接 觸點。第一導電纖維120和第二導電纖維130因為互相接 職而彼此掌通，所以會在接觸點間形成多個局部的並聯電 阻，改變原先^電流在導電纖維中導電路徑，使得雙包繞導 ， 、電紗線的電阻降低。因此，雙包繞導電紗線拉伸時，電阻 會降低。同樣原理，當紗線由拉伸狀態回復到原狀態時， 電阻會升高。 φ 單包繞導電紗線顧名思義則是在不導電的彈性紗線外 僅包繞一條導電纖維。因此，需要至少兩條相鄰之單包繞 導電紗線’以利用相鄰單包繞導電紗線上之導電纖維之接 觸點多寡的變化來反映出單包繞導電紗線的形變。如第2八 圖所示，在第一彈性紗線210和第二彈性紗線22〇外各自 鬆鬆的包繞第一導電纖維230和第二導電纖維24〇上，第 一導電纖維230和第二導電纖維240袜此沒有接觸。如第 2B圖所示，當對單包繞導電紗線施力時，第一彈性紗線2⑺ • #第二彈性紗線220會因為受力而拉長。原本鬆鬆的包繞 在第一彈性紗線210上的第一導電纖維23〇 _ : 與第一彈性炒線21〇貼緊。同樣的，包繞在第二 也會因為受力而與第二彈性紗線22()貼緊。原先不接觸 的第一導電纖維230和第二導電纖維24〇因為受力而彼此 接觸而互相導通，形成多個接觸點，同時也形成多個局部 的並聯電阻，因此電阻值較低。 無論是雙包繞導電紗線的架構或是單包繞導電紗線的 架構，皆可利用梭織法或針織法來織造導電織物。惟單包 1294000 繞導電紗線的架構中，因為至少需要兩條包繞導電紗線彼 此相鄰，所以在以針織法來織造導電織物，是採用兩條以 上單包繞導電紗線合併為單線的方式來織造。 當導電織物面積太大時，導電織物上的電流訊號容易 因為傳遞路徑過長，傳遞路徑上之電阻值過大，造成訊號 衰竭。因此，可在導電織物上間隔織入一個以上低電阻導 電纖維。如第3圖所示，低電阻導電纖維320與包繞導電 紗線310垂直相交，與包繞導電紗線31〇上的導電纖維互 相接觸，可將電流訊號導出以方便偵測。在其他實施例中， 低電阻導電纖維與包繞導電紗線可以非平行的任意角度彼 此相接觸，而非限制於圖中的垂直相交。 本發明偵測形變之導電織物可應用在呼吸頻率偵測 上。如第4圖所示，呼吸頻率偵測裝置包含導電織物400、 偵測電路410和呼吸頻率計算電路42〇(如微電腦）。導電織 物具有彈性可自由拉伸。將此導電織物貼身穿於身上，導 電織物會隨著人呼吸時胸腔和腹腔之規律起伏而規律地產 生拉伸形隻，使導電織物的電阻產生變化。導電織物電阻 的變化可經由一個與導電織物電性相接的偵測電路來偵 測’再由微電腦計算其變化的頻率，就可得到人體呼吸的 頻率。此外’也可在導電織物中加入兩個以上的可偵測呼 吸的織物電極，用以接收使用者體表電位資訊，如心跳次 數。 在較佳的實施例中，偵測電路有兩種，一種包括操作 &大電路H織物上電阻的改變造成電流微小的變化， 1294000 可經由操作放大電路放大為高低起伏的電壓訊號的變化。 另一種偵測電路則包括電阻電容充放電路。當電阻電容充 放電路和導電織物相接時，導電織物上電阻的變化會影響 到電阻電容充放電路之充放電的頻率。所以，可藉由電阻 電谷充放電路之充放電頻率的變化得到導電織物上電阻的 變化。 導電織物可因應需要織成束腹帶，嬰兒服、胸罩、孕 • 婦裝、床單或枕頭等。或是基於觸感的考量，可將導電織 物藏於衣物表布的内側。 第5圖為利用本發明之較佳實施例的呼吸頻率偵測裝 置偵測到的男童呼吸訊號圖。在這個實施例中，是將導電 織物作成束腹帶圍在男童的腹部上，測試男童侧睡時的呼 吸頻率。一般8〜14歲的男童每分鐘的呼吸頻率約為16〜2〇 次，偵測得到男童的呼吸頻率約為每分鐘175次，兩者的 數值相备接近。第6 ®是用|S]樣的束腹帶測試成人女性在 • 看書時的呼吸訊號，正常成人在平靜的狀態下每分鐘的呼 吸頻率約為16〜20次，伯測得成人女性在看書時其呼吸頻 率約為22次，兩者的數值亦相當接近。 第7圖為用本發明之較佳實施例的呼吸頻率偵測裝置 偵測到的嬰兒呼吸訊號圖。在這個實施例中，是將導電織 物作成嬰兒枕頭，測得嬰兒每分鐘的呼吸頻率每分鐘約為 16次。 由上述本發明較佳實施例可知，應用本發明具有下列 1294000 (1) 導電織物可以針織法或梭織法來織造，在織造方 式上具有相當大的彈性。 (2) 導電纖維織成的導電織物成本低廉。 (3) 偵測方式簡易，實用性高，可用來預防嬰兒猝死 以及監測睡眠時是否有呼吸中斷現象來監測睡眠 的品質 雖然本發明已以一較佳實施例揭露如上，然其並非用 以限定本發明，任何熟習此技藝者，在不脫離本發明之精 神和範圍内，當可作各種之更動與潤飾，因此本發明之保 護範圍當視後附之申請專利範圍所界定者為準。 【圖式簡單說明】 為讓本發明之上述和其他目的、特徵、優點與實施例 能更明顯易懂，所附圖式之詳細說明如下： 第1A圖係繪示依照本發明較佳實施例的一種雙包繞 導電紗線（未施力）。 第1B圖係繪示依照本發明較佳實施例的一種雙包繞 導電紗線（施力）。 第2A圖係繪示依照本發明較佳實施例的一種單包繞 導電紗線（未施力）。 第2B圖係繪示依照本發明較佳實施例的一種單包繞 導電紗線（施力）。 第3圖係繪示依照本發明較佳實施例的一種導電織物 的示意圖。 π l294〇〇〇 第4圖係繪示依照本發明較佳實施例的一種呼吸頻率 偵測襞置的架構圖。 “ 第5圖係本發明之較佳實施例的呼吸頻率偵測裝置所 该測到的男童呼吸訊號圖。 第6圖係本發明之較佳實施例的呼吸頻率偵測裝置所 摘测到的成人女性在看書時呼吸訊號圖。 第7圖係本發明之較佳實施例的呼吸頻率偵測裝置所 债測到的嬰兒呼吸訊號圖。 【主要元件符號說明】 120、230 :第一導電纖維 210 :第一彈性紗線 300 :導電織物 320 :低電阻導電纖維 410 :偵測電路 110 :彈性紗線 130 ' 240 :第二導電纖維 220 :第二彈性紗線 310 :包繞導電紗線 4〇0 :導電織物 420 :呼吸頻率計算電路 121294000 IX. Description of the Invention: TECHNICAL FIELD OF THE INVENTION The present invention relates to a conductive fabric, and more particularly to a conductive fabric capable of extracting deformation. [Prior Art] The fabrics of the measured deformation are widely used, and can be used to measure the magnitude of the external force and the frequency of the external force. Since the deformed fabric is a resilient fabric, the fabric that is different from the other sensors can detect the deformed fabric and can be placed on the object to measure the volume change and the frequency of the change. Conventional fabrics that detect deformation are woven into an optical fiber in an elastic fabric. When the elastic fabric is deformed by an external force, the bending angle of the optical fiber in the elastic fabric also changes, thereby affecting the transmission of light in the optical fiber. The magnitude and frequency of the external force are obtained by detecting the change in the signal strength of the light. The disadvantage of using fiber detection is that the cost of the fiber itself is high, and the signal device for detecting light is too complicated. And if the fabric is too deformed, it will cause the fiber to bend too much, so that the fiber is broken. Another type of detecting device is to weave a metal coil into an elastic fabric, and a current is applied to the metal coil to cause the metal coil to induce a magnetic field. When the elastic fabric is placed on an object with a regular volume change, the volume change of the object affects the strength of the magnetic field. By detecting the frequency of the change of the magnetic field strength, information related to the volume change of the object is obtained. The disadvantage of using metal coils is that they are susceptible to external magnetic fields that interfere with the accuracy of their measurements. In addition, whether it is a metal coil or an optical fiber, it is easy to deform and deteriorate after washing with 1294,000. SUMMARY OF THE INVENTION Therefore, one of the objects of the present invention is to provide a conductive fabric for detecting deformation, and to measure the magnitude and frequency of deformation of an object by using a change in resistance of the conductive fabric, and the detection method is simple and practical. Another object of the present invention is to provide a respiratory frequency detecting device which can reduce the frequency of breathing by measuring the change in electrical resistance of the conductive fabric, and can be used to prevent sudden death of the baby and to monitor whether there is a respiratory interruption during sleep. To monitor the quality of sleep. According to the above object of the present invention, a conductive fabric for detecting deformation includes at least one wrapped conductive yarn, and the wrapped conductive yarn is composed of at least one conductive fiber wrapped around an elastic yarn. When the conductive yarn is deformed by an external force, the conductive fibers form a plurality of contact points with each other, and the electric resistance of the conductive fabric also changes. According to the above object of the present invention, a conductive fabric for detecting deformation comprises at least two wrapped conductive yarns, each of which is composed of a conductive fiber wrapped around an elastic yarn, and is wrapped around the conductive yarn. When the yarn is deformed by an external force, a plurality of contact points are formed between the adjacent conductive fibers on the conductive yarn, and the electrical resistance of the conductive fabric changes. In accordance with the above objects of the present invention, a respiratory frequency detecting apparatus comprising the above-described conductive fabric and sensing circuit is provided. The conductive fabric described above is attached to a user such that the breathing of the user causes the conductive fabric to deform and change its electrical resistance. The detection circuit is used to detect the frequency of change of the resistance of the conductive 1294000 to obtain the breathing frequency of the user. - The above-described conductive fabric for detecting deformation of the present invention is characterized in that the magnitude and frequency of deformation of the object are measured by the change in electrical resistance of the conductive fiber. With a simple sensitivity detection circuit, it can be applied, for example, to monitor the respiratory rate. Therefore, y is used to monitor the quality of sleep by using the device provided by the present invention to (4) sudden death of the infant and monitoring whether there is a respiratory interruption during sleep. [Embodiment] The conductive fabric of the stripped deformation of the present invention mainly comprises two kinds of structures surrounding the conductive yarns, one of which is double-wrap, one of which is single-turn, and the % is as shown in FIG. 1a. For the double-wound conductive yarn, at least two conductive fibers are wrapped around the non-conductive elastic yarn 110. As indicated by the first conductive fibers 120 and the first, electrical fibers 13A, the first conductive fibers are interlaced with the elastic yarns 110 by the turns of the second conductive fibers 130. Because the first conductive fiber 120 and the second conductive fiber 13() are loosely wrapped, not only the first conductive fiber 120 and the second conductive fiber and the dimension 13 () are not closely attached to the elastic yarn, _ 12 () and the second conductive fibers i3G are also not connected to each other. In a preferred embodiment, the electrically conductive fibers are carbon black fibers, copper ion fibers or plated fibers. The specific resistance of the conductive fibers is preferably about A 1 〇 2 to 106 Ohms/cm. As shown in FIG. 1B, when the double-wound conductive yarn is applied, the seven yarns 110 are subjected to force. ,,., and stretched. In addition, the first conductive fiber 120 and the second conductive fiber 13" that are originally loosely wrapped around the expensive yarn 110 are in close contact with the elastic yarn 11G because of the force applied, so that the first conductive fiber ^ 7 1294000 and The 'one conductive fiber 130' is in contact with each other' to form a plurality of contact points therebetween. The first conductive fiber 120 and the second conductive fiber 130 are mutually hand-held because they are in contact with each other, so that a plurality of local parallel resistances are formed between the contact points, and the current path of the current in the conductive fibers is changed, so that the double-wrap guide , the electrical resistance of the electric yarn is reduced. Therefore, when the double-wound conductive yarn is stretched, the electric resistance is lowered. By the same principle, when the yarn returns from the stretched state to the original state, the electrical resistance rises. φ Single-wound conductive yarns, as the name suggests, enclose only one conductive fiber outside the non-conductive elastic yarn. Accordingly, at least two adjacent single-wound conductive yarns are required to reflect the deformation of the single-wound conductive yarn by utilizing variations in the number of contacts of the conductive fibers on the adjacent single-wound conductive yarn. As shown in FIG. 2, the first conductive fiber 230 and the second conductive fiber 230 are loosely wrapped around the first elastic yarn 210 and the second elastic yarn 22, respectively, and the first conductive fiber 230 and The second conductive fiber 240 socks are not in contact. As shown in Fig. 2B, when a single wrapped conductive yarn is applied, the first elastic yarn 2 (7) • #2 elastic yarn 220 is elongated due to the force. The first conductive fiber 23? _ which is originally loosely wrapped around the first elastic yarn 210 is in close contact with the first elastic frying wire 21?. Similarly, the second winding will also be in contact with the second elastic yarn 22() due to the force. The first conductive fibers 230 and the second conductive fibers 24, which are not in contact with each other, are in contact with each other by force, and are electrically connected to each other to form a plurality of contact points, and a plurality of local parallel resistors are also formed, so that the resistance value is low. Whether it is a double-wound conductive yarn structure or a single-wound conductive yarn structure, the conductive fabric can be woven by a weaving method or a knitting method. However, in a single package of 1294000 winding conductive yarns, since at least two wrapped conductive yarns are required to be adjacent to each other, in the weaving of the conductive fabric by knitting, two or more single-wound conductive yarns are combined into a single wire. The way to weave. When the area of the conductive fabric is too large, the current signal on the conductive fabric is easy because the transmission path is too long, and the resistance value on the transmission path is too large, causing signal failure. Therefore, more than one low-resistance conductive fiber can be woven on the conductive fabric at intervals. As shown in Fig. 3, the low-resistance conductive fiber 320 is perpendicularly intersected with the wrapped conductive yarn 310, and is in contact with the conductive fibers wrapped around the conductive yarn 31, and the current signal can be derived for easy detection. In other embodiments, the low resistance conductive fibers are in contact with each other at any angle that may be non-parallel to the wrapped conductive yarns, and are not limited to vertical intersections in the figures. The conductive fabric for detecting deformation in the present invention can be applied to respiratory frequency detection. As shown in FIG. 4, the respiratory rate detecting device includes a conductive fabric 400, a detecting circuit 410, and a respiratory frequency calculating circuit 42 (such as a microcomputer). The conductive fabric has elasticity and can be freely stretched. The conductive fabric is put on the body, and the conductive fabric will be stretched and shaped according to the regular fluctuation of the chest cavity and the abdominal cavity when the person breathes, so that the resistance of the conductive fabric changes. The change in the resistance of the conductive fabric can be detected by a detection circuit electrically connected to the conductive fabric, and then the frequency of the change is calculated by the microcomputer to obtain the frequency of the human body's breathing. In addition, more than two fabric electrodes capable of detecting respiration can be added to the conductive fabric to receive information on the body surface potential of the user, such as the number of heartbeats. In a preferred embodiment, there are two types of detection circuits, one of which includes a change in the resistance of the large circuit H fabric to cause a slight change in current, and the 1294000 can be amplified by amplifying the voltage signal into a high and low fluctuation voltage signal. Another detection circuit includes a resistor-capacitor charging and discharging circuit. When the resistor-capacitor charging and discharging circuit is connected to the conductive fabric, the change in resistance on the conductive fabric affects the frequency of charging and discharging of the resistor-capacitor charging and discharging circuit. Therefore, the change in the resistance of the conductive fabric can be obtained by the change of the charging and discharging frequency of the electric resistance charging and discharging circuit. Conductive fabrics can be woven into corsets, baby clothes, bras, maternity, bed sheets or pillows. Or based on the feel of the touch, the conductive fabric can be hidden inside the cloth. Fig. 5 is a diagram showing the respiratory signal of a boy detected by the respiratory frequency detecting device of the preferred embodiment of the present invention. In this embodiment, the conductive fabric is placed around the boy's abdomen as a corset, and the frequency of breathing of the boy while sleeping is tested. Generally, the breathing rate of a boy aged 8 to 14 is about 16 to 2 times per minute. The respiratory rate of the boy is about 175 times per minute. The values of the two are close. The 6th ® is a |S]-like corset belt to test the respiratory signal of an adult woman during reading. The normal adult has a respiratory rate of about 16 to 20 times per minute in a calm state. The adult female is reading a book. The respiratory rate is about 22 times, and the values of the two are quite close. Fig. 7 is a diagram showing the baby's respiratory signal detected by the respiratory frequency detecting device of the preferred embodiment of the present invention. In this embodiment, the conductive fabric is made into a baby pillow, and the baby's respiratory rate per minute is measured to be about 16 times per minute. As is apparent from the above preferred embodiments of the present invention, the present invention has the following 1294000 (1) The conductive fabric can be woven by knitting or weaving, and has considerable elasticity in the weaving method. (2) Conductive fabric woven from conductive fibers is inexpensive. (3) The detection method is simple and practical, and can be used to prevent sudden death of the baby and to monitor whether there is a breathing interruption during sleep to monitor the quality of sleep. Although the present invention has been disclosed above in a preferred embodiment, it is not limited thereto. In the present invention, it is to be understood that the scope of the invention is defined by the scope of the appended claims. BRIEF DESCRIPTION OF THE DRAWINGS The above and other objects, features, advantages and embodiments of the present invention will become more <RTIgt; A double-wound conductive yarn (not forced). Fig. 1B is a diagram showing a double-wound conductive yarn (applied force) in accordance with a preferred embodiment of the present invention. Fig. 2A is a view showing a single-wound conductive yarn (not forced) in accordance with a preferred embodiment of the present invention. Figure 2B is a diagram showing a single-wound conductive yarn (applied force) in accordance with a preferred embodiment of the present invention. Figure 3 is a schematic illustration of a conductive fabric in accordance with a preferred embodiment of the present invention. π l294〇〇〇 Fig. 4 is a block diagram showing a respiratory frequency detecting device in accordance with a preferred embodiment of the present invention. Fig. 5 is a diagram showing the respiratory signal of the boy detected by the respiratory frequency detecting device of the preferred embodiment of the present invention. Fig. 6 is a view showing the respiratory frequency detecting device of the preferred embodiment of the present invention. An adult female breathes a signal map while reading a book. Fig. 7 is a diagram of a baby respiratory signal measured by a respiratory frequency detecting device according to a preferred embodiment of the present invention. [Key element symbol description] 120, 230: First conductive Fiber 210: First elastic yarn 300: Conductive fabric 320: Low-resistance conductive fiber 410: Detection circuit 110: Elastic yarn 130' 240: Second conductive fiber 220: Second elastic yarn 310: Wrapped conductive yarn 4〇0: conductive fabric 420: respiratory frequency calculation circuit 12