TWI809601B - Vascular state measuring device and method - Google Patents
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本發明係關於血管狀態量測裝置及方法;特別涉及一種磁電效應的非侵入式之血管狀態量測裝置及方法。 The present invention relates to a blood vessel state measurement device and method; in particular, it relates to a magnetoelectric effect non-invasive blood vessel state measurement device and method.
血管狀態的量測可以使用例如用於即時心率、連續血壓、心血管功能的監控等應用中。並且,為了要提高生活品質以及方便性,攜帶式或穿戴式的量測方式將漸漸成為主流,而傳統駐點式(例如,於醫療院所使用血壓機等醫療儀器)將會漸漸式微。為了達到攜帶式或穿戴式的非侵入式量測,常見的量測方式大多為利用光學或者是力學(例如,壓電轉換)作為量測機制。 The measurement of vascular status can be used, for example, in applications such as real-time heart rate, continuous blood pressure, monitoring of cardiovascular function, and the like. Moreover, in order to improve the quality of life and convenience, portable or wearable measurement methods will gradually become the mainstream, while traditional on-site measurement methods (for example, medical instruments such as blood pressure machines used in medical institutions) will gradually decline. In order to achieve portable or wearable non-invasive measurement, most common measurement methods use optics or mechanics (for example, piezoelectric conversion) as the measurement mechanism.
然而,利用光學或者是力學非常容易面臨到受到環境干擾而導致量測精確度不足的問題。並且受測者/使用者各別的差異(例如,膚色、角質厚度、體型)都會造成光學或者是力學機制量測上的誤差,導致傳統攜帶式或穿戴式的量測設備所獲得的量測數值不被信任。 However, the use of optics or mechanics is very easy to face the problem of insufficient measurement accuracy due to environmental interference. And the individual differences of the subjects/users (for example, skin color, cutin thickness, body shape) will cause errors in the measurement of optical or mechanical mechanisms, resulting in measurement errors obtained by traditional portable or wearable measurement devices. Values are not trusted.
因此,在追求裝置可以達到攜帶性或便利性的同時,能提供避免因使用者各別差異所導致的量測誤差將會是本領域技術發展的一大重點。 Therefore, while pursuing the portability or convenience of the device, it will be a major focus of technical development in this field to avoid measurement errors caused by individual differences among users.
本發明的目的之一在於提供一種避免因使用者各別差異所導致的量測誤差的非侵入式血管狀態量測裝置及方法。 One of the objectives of the present invention is to provide a non-invasive blood vessel state measurement device and method that avoids measurement errors caused by individual differences among users.
本發明提供一種血管狀態量測裝置,包含線圈組、訊號源以及處理模組。線圈組輸出第一電磁訊號至目標區域以使目標區域產生渦電流,並接收對應渦電流產生的第二電磁訊號。訊號源耦接至線圈組並輸出交流訊號至線圈組以生成所述第一電磁訊號。處理模組耦接至線圈組並根據所述第一電磁訊號及所述第二電磁訊號計算特徵訊號。其中所述特徵訊號對應於目標區域處的至少一血管的至少一狀態。 The invention provides a blood vessel state measurement device, which includes a coil group, a signal source and a processing module. The coil group outputs the first electromagnetic signal to the target area to generate eddy current in the target area, and receives the second electromagnetic signal generated corresponding to the eddy current. The signal source is coupled to the coil set and outputs an AC signal to the coil set to generate the first electromagnetic signal. The processing module is coupled to the coil set and calculates characteristic signals according to the first electromagnetic signal and the second electromagnetic signal. Wherein the characteristic signal corresponds to at least one state of at least one blood vessel in the target area.
本發明提供一種血管狀態量測方法,其包含:輸出第一電磁訊號至目標區域以使目標區域產生渦電流;接收對應渦電流產生的第二電磁訊號;以及根據第一電磁訊號及第二電磁訊號計算對應於目標區域處的至少一血管的至少一狀態的特徵訊號。 The present invention provides a blood vessel state measurement method, which includes: outputting a first electromagnetic signal to a target area to generate an eddy current in the target area; receiving a second electromagnetic signal corresponding to the eddy current; and according to the first electromagnetic signal and the second electromagnetic signal The signal calculation is a characteristic signal corresponding to at least one state of at least one blood vessel in the target area.
如上所述,透過線圈組輸出電磁訊號以使目標區域內的血管產生磁電效應。磁電效應可以有效地避免因為受測者/使用者各別的差異所產生的量測誤差。 As mentioned above, the electromagnetic signal is output through the coil group to cause the blood vessels in the target area to generate magnetoelectric effect. The magnetoelectric effect can effectively avoid the measurement errors caused by the individual differences of the subjects/users.
100:血管狀態量測裝置 100: Vascular state measuring device
110:線圈組 110: coil group
120:訊號源 120: signal source
130:處理模組 130: Processing module
140:匹配元件 140: Matching components
150:深度偵測模組 150: Depth detection module
160:通訊模組 160: Communication module
170:阻隔元件 170: barrier element
171:缺口 171: Gap
500:電子裝置 500: electronic device
MS1:第一電磁訊號 MS1: First Electromagnetic Signal
MS2:第二電磁訊號 MS2: Second Electromagnetic Signal
TA:目標區域 TA: target area
AS:交流訊號 AS: AC signal
FS:特徵訊號 FS: characteristic signal
I:渦電流 I: eddy current
V:血管 V: blood vessel
圖1為本發明一實施例中,血管狀態量測裝置的示意圖。 FIG. 1 is a schematic diagram of a blood vessel state measuring device according to an embodiment of the present invention.
圖2為本發明一實施例中,血管特徵訊號量測的訊號圖。 FIG. 2 is a signal diagram of blood vessel characteristic signal measurement in an embodiment of the present invention.
圖3為本發明一實施例中,設置匹配元件的示意圖。 FIG. 3 is a schematic diagram of setting a matching element in an embodiment of the present invention.
圖4為本發明一實施例中,血管狀態量測裝置量測血管深度的示意圖。 FIG. 4 is a schematic diagram of a blood vessel state measuring device measuring blood vessel depth according to an embodiment of the present invention.
圖5為本發明一實施例中,血管狀態量測裝置耦接至電子裝置的示意圖。 FIG. 5 is a schematic diagram of a blood vessel state measuring device coupled to an electronic device according to an embodiment of the present invention.
圖6為本發明一實施例中,阻隔元件設置的示意圖。 FIG. 6 is a schematic diagram of an arrangement of barrier elements in an embodiment of the present invention.
圖7A-7C為本發明一實施例中,血管狀態量測方法的流程圖。 7A-7C are flowcharts of a method for measuring a blood vessel state in an embodiment of the present invention.
呈現附圖以幫助描述本發明的各個方面,為簡化附圖及突顯附圖所要呈現之內容,附圖中習知的結構或元件將可能以簡單示意的方式繪出或是以省略的方式呈現。例如,元件的數量可以為單數亦可為複數。提供這些附圖僅僅是為了解說這些方面而非對其進行限制。 The drawings are presented to help describe various aspects of the present invention. In order to simplify the drawings and highlight the content to be presented in the drawings, the known structures or elements in the drawings may be drawn in a simple schematic manner or presented in an omitted manner . For example, the number of elements may be singular or plural. These figures are provided merely to illustrate these aspects and not to limit them.
對本文中使用諸如「第一」、「第二」等名稱的元件的任何引用通常不限制這些元件的數目或順序。相反,這些名稱在本文中用作區分兩個或更多個元件或元件實例的便利方式。因此,應當理解的是,請求項中的名稱「第一」、「第二」等不一定對應於書面描述中的相同名稱。此外,應當理解的是,對第一和第二元件的引用並不表示只能採用兩個元件或者第一元件必須在第二元件之前。關於本文中所使用之『包含』、『包括』、『具有』、『含有』等等,均為開放性的用語,即意指包含但不限於。 Any reference to an element herein using a designation such as "first," "second," etc. generally does not limit the number or order of those elements. Rather, these designations are used herein as a convenient way of distinguishing between two or more elements or instances of an element. Therefore, it should be understood that designations "first", "second", etc. in the claims do not necessarily correspond to the same designations in the written description. Furthermore, it should be understood that reference to first and second elements does not mean that only two elements may be used or that the first element must precede the second element. "Includes", "including", "has", "containing" and so on used in this article are all open terms, meaning including but not limited to.
術語「耦接」在本文中用於指代兩個結構之間的直接或間接電耦接。例如,在間接電耦接的一個示例中,一個結構可以經由電阻器、電容器或電感器等被動元件被耦接到另一結構。 The term "coupled" is used herein to refer to a direct or indirect electrical coupling between two structures. For example, in one example of indirect electrical coupling, one structure may be coupled to another structure via a passive element such as a resistor, capacitor, or inductor.
在本發明中,詞語「示例性」、「例如」用於表示「用作示例、實例或說明」。本文中描述為「示例性」、「例如」的任何實現或方面不一定被 解釋為比本發明的其他方面優選或有利。如本文中關於規定值或特性而使用的術語「大約」、「大致」旨在表示在規定值或特性的一定數值(例如,10%)以內。 In the present invention, the words "exemplary" and "for example" are used to mean "serving as an example, instance or illustration". Any implementation or aspect described herein as "exemplary", "such as" is not necessarily construed as preferred or advantageous over other aspects of the invention. The terms "about" and "approximately" as used herein with respect to a stated value or characteristic are intended to mean within a certain value (eg, 10%) of the stated value or characteristic.
在本發明中,文中所指的「血管狀態」例如但不限於,血管收縮及/或舒張、血管彈性、血管內狀態(例如,血管內部是否堵塞或暢通、血流狀態等)、血管增生、血管密度、血管壁狀態(例如,血管壁是否破損)。 In the present invention, the "vascular state" referred to herein is, for example but not limited to, vasoconstriction and/or dilation, vascular elasticity, intravascular state (for example, whether the inside of the blood vessel is blocked or smooth, blood flow state, etc.), vascular hyperplasia, Vessel density, vessel wall state (eg, whether the vessel wall is damaged).
請參照圖1,圖1說明一種血管狀態量測裝置100,包含線圈組110、訊號源120以及處理模組130。線圈組110輸出第一電磁訊號MS1至目標區域TA以使目標區域TA產生渦電流I,並接收對應渦電流I產生的第二電磁訊號MS2。訊號源120耦接至線圈組110並輸出交流訊號AS至線圈組110以生成第一電磁訊號MS1。處理模組130耦接至線圈組110並根據第一電磁訊號MS1及第二電磁訊號MS2計算特徵訊號FS。其中特徵訊號FS對應於目標區域TA處的至少一血管的至少一狀態。
Please refer to FIG. 1 . FIG. 1 illustrates a blood vessel state measuring
具體來說,訊號源120可以是透過主動元件(例如,震盪器、計時器)及/或被動元件(例如,電阻、電容)所整合於印刷電路板上所構成的交流訊號產生器,或是任意習知的交流訊號產生的裝置或設備。而處理模組130可以是利用微處理器、現場可程式邏輯閘(FPGA)、專用積體電路(ASIC)等具運算或程式化能力等元件所形成之模組,或是任意具有運算或程式執行能力的裝置或設備。須說明的是,訊號源可以透過處理模組進行控制,或是透過訊號源所耦接接的任一控制元件來進行控制。
Specifically, the
訊號源120提供交流訊號AS至線圈組110,線圈組110因為電磁效應而生成第一電磁訊號MS1。線圈組110具體來說是設置於目標區域TA的
外側。大致來說,線圈組110的設置位置與方向係能將第一電磁訊號MS1大部分的能量傳輸至目標區域TA的血管V上。於一較佳實施例中,線圈組110的設置角度為將第一電磁訊號MS1的發射方向以覆蓋目標區域TA的血管V內血流較大體積(或截面積)為目標。此外,雖然圖1僅繪製出一組線圈組110,然而本發明的線圈組110並不限於其形狀(例如,可以為圓形、橢圓形、方形等)或數量(例如,兩個線圈分別產生兩個磁場(例如,兩個線圈接收兩種不同的交流訊號或同一種交流訊號))。可以依據設置區域以及不同需求來選擇不同的線圈形狀或數量。
The
線圈組110輸出第一電磁訊號MS1至目標區域TA以使目標區域TA產生渦電流I,具體來說,第一電磁訊號MS1施加至目標區域TA後,目標區域TA(例如,目標區域TA處的組織、血管或血液等可視為平面導體物)會因為第一電磁訊號MS1而相應產生渦電流I。渦電流I將會產生與第一電磁訊號MS1的磁場方向相反的第二電磁訊號MS2。第二電磁訊號MS2將會被線圈組110所接收(即,第二電磁訊號MS2在線圈組110上產生磁電效應)而產生感應交流訊號。處理模組130將會量測感應交流訊號並產生特徵訊號FS。舉例來說,特徵訊號FS可以為量測到的線圈組110的阻抗變化量、或是第一電磁訊號MS1因為受第二電磁訊號MS2影響而產生的變化量。此外,也可以透過直接量測第二電磁訊號MS2的數值(例如,頻率變化量、振幅變化量)作為特徵訊號FS。特徵訊號FS例如可以對應血管V內的血液量的增加或減少(例如,依據血管V的收縮及舒張而導致血管V內的血液量增加及/或減少)。舉例來說,請參照圖2,圖2為以線圈組110的阻抗變化量(Y軸)作為特徵訊號FS的示例。當血管收縮及/或舒張時,目標區域TA內的因為第一電磁訊號MS1所產生的渦
電流I也隨之變化(例如,因為血管收縮/舒張時,血管內血液量變化導致),而導致因為渦電流I而產生的第二電磁訊號MS2也產生相對的變化量。此時,線圈組110接收到第二電磁訊號MS2後,第二電磁訊號MS2導致處理模組130量測線圈組110的阻抗值產生變化量(此時,處理模組130可以為阻抗計)。然而上述實施例僅是示例,並非用於限制本發明所量測之血管狀態以及量測機制。
The
於一實施例中,血管狀態量測裝置還包含匹配元件。請參照圖3,匹配元件140設置於線圈組110與目標區域TA之間。匹配元件140的磁阻抗介於目標區域TA的磁阻抗與線圈組110的磁阻抗之間。具體來說,位於目標區域TA的血管(例如,動脈),當線圈組110貼附於最接近目標區域TA的位置時,匹配元件140可以設置於線圈組110與目標區域TA外側的皮膚S(或者,衣物、障礙物)之間。較佳而言,匹配元件140的磁阻抗可介於目標區域TA至皮膚S(或者,衣物、障礙物)的等效磁阻抗與線圈組110至匹配元件140之間介質的等效磁阻抗之間。藉此減少第一電磁訊號MS1與第二電磁訊號MS2能量傳遞時的能量損耗,以達到使用較小的能量便能達到量測到所需訊號或提高訊雜比之目的。避免過大的能量造成受測者受傷或者裝置的續航力不足等問題。然而,設置匹配元件140的目的並不限於上述舉例。
In one embodiment, the blood vessel state measuring device further includes a matching element. Referring to FIG. 3 , the
於一實施例中,請參照圖4,血管狀態量測裝置100還包含經組態以發出偵測訊號DS至目標區域TA並提供對應該至少一血管V的深度資訊DI至訊號源120的深度偵測模組150,以使訊號源120可以依據深度資訊DI調整交流訊號AS的頻率及/或振幅。或是深度偵測模組150將深度資訊DI提供至控制模組130,以使控制模組130調整線圈組110的阻抗(例如,透過調整線圈組110的電容值及/或電感值)。舉例來說,深度偵測模組150可以為光學(偵
測訊號為光訊號)或是聲學(偵測訊號為聲波訊號)等具穿透性(例如,穿透皮膚或衣物)的偵測機制之元件所構成之模組。透過例如飛時測距(TOF)等測距機制來量測目標區域中血管的深度,並將此深度資訊DI提供給訊號源120的控制元件(此實施例中為處理模組130),處理模組130依據深度資訊DI調整訊號源120所輸出的交流訊號AS的頻率及/或振幅,或是調整調整線圈組110的電容值及/或電感,以達到較佳的效果(例如,產生較大的渦電流I或是接收到較大的第二電磁訊號MS2等效果)。
In one embodiment, please refer to FIG. 4 , the blood vessel
於調整線圈組110的電容值及/或電感的實施例中,線圈組可例如耦接至可調整式電容器及/或電感器。具體來說,當訊號源120輸出交流訊號AS前,調整可調整式電容器及/或電感器的數值以獲得最大響應(例如,使線圈組110的電容值及/或電感值遞增或遞減以進行最合適電容值及/或電感值範圍的掃描),或是根據深度偵測模組150所獲得的深度資訊DI,來調控線圈組110的電容值及/或電感值(例如,建立深度-阻抗值對應表單,當得知血管深度時,採用已知的合適阻抗值進行量測),或是上述方法的混用。於此實施例中,訊號源120可以提供固定頻率的交流訊號AS,而僅改變線圈組110的電容與電感值的比例(LC值)進而達到調整第一電磁訊號MS1的效果。透過調整可調整式電容器的電容值使得第一電磁訊號MS1輸出至目標區域TA後能產生較大的響應(即,較大的渦電流I產生或是較大的第二電磁訊號MS2)。
In an embodiment where the capacitance and/or inductance of the coil set 110 is adjusted, the coil set may, for example, be coupled to an adjustable capacitor and/or inductor. Specifically, before the
然而,調整訊號源120所輸出的交流訊號AS的機制並不受限於需要接收深度偵測模組150所提供的深度資訊DI。於一實施例中,血管狀態量測裝置100於訊號源120輸出交流訊號AS前,訊號源120輸出對應一頻率區間的頻率掃描訊號,交流訊號AS輸出時的頻率可選自頻率掃描訊號中,產生響應
最大者之頻率。具體來說,訊號源120在可能的頻率區間(例如,千赫茲至百萬赫茲)依序輸出不同頻率的交流訊號(例如,以頻率遞增或遞減的方式)。掃描不同頻率的交流訊號可能會使目標區域TA產生不同大小的渦電流I,以及對應產生不同大小的響應(例如,產生不同大小的第二電磁訊號MS2)。處理模組130可以根據線圈組110所接收到的響應中,響應最大或最佳者所對應的發射頻率,來決定訊號源120所輸出的交流訊號AS的頻率。藉此,可以(例如但不限於)使血管狀態量測裝置100以較適配的交流訊號AS進行量測以獲得較佳的效果(例如,較好的訊雜比)。
However, the mechanism for adjusting the AC signal AS output by the
於一實施例中,如圖5所示,血管狀態量測裝置100還包括耦接至處理模組130並經組態以輸出特徵訊號FS至電子裝置500的通訊模組160。具體來說,電子裝置500例如為智慧型手機、桌上型電腦、筆記型電腦等後端裝置。通訊模組160透過無線(例如,藍芽、無線網路、紅外線等)或者有線(例如,有線網路或纜線等)與電子裝置500通訊並提供特徵訊號FS給電子裝置500。電子裝置500內可以安裝應用程式來記錄或分析特徵訊號FS。藉此可以達到追蹤或者是評估血管狀態之目的,但不限於此。
In one embodiment, as shown in FIG. 5 , the blood vessel
於一實施例中,請參照圖6,血管狀態量測裝置100還包括阻隔元件170。阻隔元件170設置於線圈組110與目標區域TA之間(可以單獨設置或是與匹配元件140一起設置)。阻隔元件170具有缺口171。第一電磁訊號MS1指向目標區域TA的第一部分P1可以通過缺口171(並未受到阻隔),且阻隔元件170阻隔第一電磁訊號MS1未通過缺口171的第二部分P2(受到阻隔元件170阻隔而無法穿透)。具體來說,阻隔元件170的材料為電導體或磁導體材料或其他可阻隔電磁波之材料。第一電磁訊號MS1雖然由線圈組110朝目標
區域TA而發出。但第一電磁訊號MS1依然有發散(例如,因磁力線發散並未指向目標區域TA)的部分(即,第二部分P2)。因此,第一電磁訊號MS1的第二部分P2並未完整地(或無法)作用在目標區域TA上,而可能產生雜訊。所產生的雜訊可能會干擾第一電磁訊號MS1的第一部分P1(第一電磁訊號朝目標區域發送且並未發散的部分)及/或渦電流I響應產生的第二電磁訊號MS2。於此實施例中,透過阻隔元件170的缺口171,可以使第一電磁訊號MS1的第一部分P1通過阻隔元件170而不被阻隔元件170所屏蔽,而第一電磁訊號MS1的第二部分P2將被阻隔元件170所屏蔽。藉由設置阻隔元件170,可以達到(例如)提高訊雜比之目的。此外,缺口171可以根據線圈組110的形狀選擇圓形缺口、方形缺口或其他形狀。須說明的是,缺口171的形狀及/或設置位置可以依照實際需求而有所調整。
In an embodiment, please refer to FIG. 6 , the blood vessel
請參照圖7A,說明一種血管狀態量測方法。步驟S1:輸出第一電磁訊號至目標區域以使目標區域產生渦電流;步驟S2:接收對應渦電流產生的第二電磁訊號;以及步驟S3:根據第一電磁訊號及第二電磁訊號計算對應於目標區域處的至少一血管的至少一狀態的特徵訊號。另外,於一實施例中,可以包括步驟S4:輸出該特徵訊號至電子裝置,以進行後續運算或統計。 Referring to FIG. 7A , a method for measuring a blood vessel state is illustrated. Step S1: output the first electromagnetic signal to the target area to generate eddy current in the target area; step S2: receive the second electromagnetic signal corresponding to the eddy current; and step S3: calculate the corresponding A characteristic signal of at least one state of at least one blood vessel in the target area. In addition, in an embodiment, step S4 may be included: outputting the feature signal to an electronic device for subsequent calculation or statistics.
於一實施例中,請參照圖7B,圖7B說明步驟S1輸出第一電磁訊號至目標區域之前,還可以有步驟S1-1:設置匹配元件於第一電磁訊號的輸出端與目標區域之間以降低輸出端與目標區域之間的電磁阻抗差異。此外,在步驟S1-1中,也可以設置阻隔元件於第一電磁訊號的輸出端與目標區域之間。阻隔元件具有缺口,第一電磁訊號指向目標區域的第一部分可以通過缺口,且阻隔元件阻隔第一電磁訊號未通過缺口的第二部分。換句話說,第一部分因為缺口並 未受到阻隔元件的阻隔,可以傳遞至目標區域。而第二部分因受到阻隔元件的阻隔,並未傳遞至目標區域。須說明的是,匹配元件以及阻隔元件可以一起設置,或者單獨設置,可以依照實際需求有所調整。本發明並不受限。 In one embodiment, please refer to FIG. 7B. FIG. 7B illustrates that before step S1 outputs the first electromagnetic signal to the target area, there may also be a step S1-1: setting a matching element between the output end of the first electromagnetic signal and the target area To reduce the difference in electromagnetic impedance between the output and the target area. In addition, in step S1-1, a blocking element may also be disposed between the output end of the first electromagnetic signal and the target area. The blocking element has a gap, the first part of the first electromagnetic signal directed to the target area can pass through the gap, and the blocking element blocks the second part of the first electromagnetic signal not passing through the gap. In other words, the first part because the gap does not Unblocked by barrier elements, it can be delivered to the target area. However, the second part is not delivered to the target area because it is blocked by the blocking element. It should be noted that the matching element and the blocking element can be set together or separately, and can be adjusted according to actual needs. The present invention is not limited.
於一實施例中,請參照圖7C,圖7C說明步驟S1輸出第一電磁訊號至目標區域之前,還可以有步驟S1-2:調整及/或優化第一電磁訊號的輸出參數。舉例來說,於一實施例中,可以量測對應目標區域中血管的深度資訊,並依據深度資訊調整第一電磁訊號的頻率或振幅。於一實施例中,可以輸出對應一頻率區間的頻率掃描電磁訊號,第一電磁訊號的頻率選自頻率掃描電磁訊號中響應最大者之頻率。於一實施例中,可以透過改變線圈組的電容與電感值的比例(LC值)而達到調整及/或優化第一電磁訊號。於此實施例中,舉例來說,可以透過可以掃描電容及/或電感值或者是根據所獲得的深度資訊建立深度-LC值對應關係,使得第一電磁訊號輸出至目標區域後能產生較大的響應(即,較大的渦電流產生或是較大的第二電磁訊號)。此外,步驟S1-2可以在量測過程中,依據實際量測結果(例如,特徵訊號的訊雜比)動態地調整調整及/或優化第一電磁訊號的輸出參數。 In one embodiment, please refer to FIG. 7C . FIG. 7C illustrates that before step S1 of outputting the first electromagnetic signal to the target area, there may be step S1-2: adjusting and/or optimizing the output parameters of the first electromagnetic signal. For example, in one embodiment, the depth information of blood vessels corresponding to the target area can be measured, and the frequency or amplitude of the first electromagnetic signal can be adjusted according to the depth information. In one embodiment, a frequency-sweeping electromagnetic signal corresponding to a frequency range may be output, and the frequency of the first electromagnetic signal is selected from the frequency with the largest response among the frequency-sweeping electromagnetic signals. In one embodiment, the adjustment and/or optimization of the first electromagnetic signal can be achieved by changing the ratio (LC value) of the capacitance to the inductance of the coil group. In this embodiment, for example, by scanning the capacitance and/or inductance values or establishing a depth-LC value correspondence relationship based on the obtained depth information, the first electromagnetic signal can generate a larger response (that is, a larger eddy current generation or a larger second electromagnetic signal). In addition, the step S1-2 can dynamically adjust and/or optimize the output parameters of the first electromagnetic signal according to the actual measurement results (for example, the signal-to-noise ratio of the characteristic signal) during the measurement process.
提供對本發明的先前描述以使得本領域具通常知識者能夠製作或實施本發明。對於本領域具通常知識者來說,對本發明的各種修改將是很清楚的,並且在不脫離本發明的精神或範圍的情況下,本文中定義的一般原理可以應用於其他變化。因此,本發明不旨在限於本文中描述的示例,而是符合與本文中發明的原理和新穎特徵一致的最寬範圍。 The previous description of the invention is provided to enable one of ordinary skill in the art to make or practice the invention. Various modifications to the invention will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other changes without departing from the spirit or scope of the invention. Thus, the present invention is not intended to be limited to the examples described herein but is to be accorded the widest scope consistent with the principles and novel features of the invention herein.
100 血管狀態量測裝置
110 線圈組
120 訊號源
130 處理模組
MS1 第一電磁訊號
MS2 第二電磁訊號
TA 目標區域
AS 交流訊號
FS 特徵訊號
I 渦電流
V 血管
100 Vascular
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CN103068302A (en) * | 2010-05-13 | 2013-04-24 | 合理医疗创新有限公司 | Method and system for using distributed electromagnetic (EM) tissue(s) monitoring |
WO2018127482A1 (en) * | 2017-01-09 | 2018-07-12 | Koninklijke Philips N.V. | Inductive sensing system for sensing electromagnetic signals from a body |
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CN103068302A (en) * | 2010-05-13 | 2013-04-24 | 合理医疗创新有限公司 | Method and system for using distributed electromagnetic (EM) tissue(s) monitoring |
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