TW201228634A - Method for assessing vascular stiffness index - Google Patents
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201228634 六、發明說明: 【發明所屬之技術領域】 本發明係有關於一種檢測方法’特別是指一種血管硬 化指標之檢測方法。 【先前技術】 動脈血管硬化(Arterial Hardening),除了老化的因素外 ’許多疾病也會造成動脈血管硬化的現象。國人十大死因 中的腦血管疾病(Cerebral Vessel Disease)、心臟病(Cardiac201228634 VI. Description of the Invention: TECHNICAL FIELD OF THE INVENTION The present invention relates to a detection method, particularly to a method for detecting a blood vessel hardening index. [Prior Art] Arterial Hardening, in addition to aging factors, many diseases can also cause arteriosclerosis. Cerebral Vessel Disease and Cardiac in the top ten causes of death of Chinese people
Disease)、糖尿病(Diabetes Mellitus)、高血壓(Hypertensi〇n) 疾病以及相當比例的腎臟病(Renal Disease)都與動脈血管硬 化有直接或間接的關係。 然而,各種外在因素(生活習慣不良,長期處於壓力下 ,或缺乏運動等)及内在因素(遺傳性疾病)的影響,都會造 成動脈血管提前硬化或產生病變。近年來,國人生活品質 提升,飲食及運動型態和以前有著極大的不同,導致許多 老年疾病的年齡層逐漸年輕化,而這些疾病大多與動脈血 官硬化有關。除了遺傳性疾病及年齡老化所引起的動脈企 官硬化外,其他後天因素所造成的動脈血管硬化,都是可 以提早預知並經由藥物、飲食或運動來控制的。有鑑於此 ,提早預知動脈血管的硬化程度有絕對的必要性。 目前已有許多的技術被用來間接估測血管硬化的程度 這二技術主要包括超音波技術(Ultrasound Echo-Tracking, Doppler)’脈波傳遞時間分析技術(八仙丨”匕TranshDisease, Diabetes Mellitus, Hypertensi〇n disease, and a significant proportion of Renal Disease are directly or indirectly related to arterial vascular hardening. However, various external factors (poor living habits, prolonged stress, lack of exercise, etc.) and intrinsic factors (hereditary diseases) can cause premature atherosclerosis or lesions. In recent years, the quality of life of Chinese people has improved, and the patterns of diet and exercise have been greatly different from those of the past. As a result, many age groups of old age diseases have gradually become younger, and most of these diseases are related to arterial cirrhosis. In addition to hereditary disease and ageing, the arteriosclerosis caused by other acquired factors can be predicted early and controlled by drugs, diet or exercise. In view of this, it is absolutely necessary to predict the degree of hardening of arterial blood vessels early. At present, many techniques have been used to indirectly estimate the degree of hardening of the arteries. These two technologies mainly include Ultrasound Echo-Tracking (Doppler)' pulse wave transit time analysis technology (Eight Immortals) 匕Transh
Tlme),阻抗式體積描述技術(Impedance Plethysomgraphy), 201228634 光學式容積描記術(Photo-Plethysmography),振盪技術 (Oscillometry),壓張技術(Tonometry),及血壓波形分析技 術(Analysis of Pressure Waveform)。 其中超音波技術可測出it液流速或血管口徑,若再加 上其它位置的血壓量測,則可推導出動脈順應性,而目前 臨床上也開發出一套針對動脈血管硬化疾病的高解析度微 小化血管超音波系統(Intravascular Ultrasound System, IVUS),在脈波傳遞時間分析技術中,則利用脈波速度 (PWV,Pulse Wave Velocity)、血管大小(r)及管壁厚度(h) 間的關係式,PWV2 = Eh / 2rp (其中p為血液密度),間接 地粗估動脈管壁的抗彈性係數⑺);其他技術如阻抗式和光 學式容積描記術’則分別利用組織的電氣特性和對特定波 長光吸收度的差異性,來間接推估血管的體積,再搭配血 壓波形,估測出血管的抗彈性力;而振盪技術和壓張技術 則分別透過血管和氣囊間流體推擠的交互作用以及施加壓 力的測量,來推估血管壁的順應性;在血壓波形分析技術 中,則是利用動脈血壓舒張期的指數形衰減現象,來推算 血管腔室的順應性。 另外也有利用小區域的壓凹技術(Indentati〇n)來測量動 脈順應性,例如我國公開公報第2〇〇91丨199號案所揭露之 内谷,係利用致動器對皮表進行逐步壓凹,以壓力感測器 測得皮表平均血壓,並以位移感測器感測此時所下壓之深 度,來得到動脈平均血壓及順應性。 然而,上述方法相當複雜,且需要多種感測設備配合 201228634 施作’不利居家或臨床上的實際應用。再者,動脈血管的 硬度並非一定值,而是會隨血管腔内血壓的大小而改變, 也就是動脈血管的硬度是血壓的函數,也是時間的函數, 而由於平均動脈血壓(Mean Arterial Pressure,MAP)是各種5| 官在生理功能運作上的依據,所以在平均動脈血壓時的動 脈血管硬化指標,不但具有重要的生理意義,也最具有參 考價值,因此,如何簡易獲得在平均動脈血壓下之動脈血 管硬化指# ’是有其必要性的。雖然市面上已經出現有包 含血管硬度參考指標的氣囊式血壓計,但在其參數的擷取 與地區性指標的真實性還是有所質疑的。 【發明内容】 因此,本發明之目的,即在提供一種利用簡易的方式 就可以量測在平均動脈血壓下的血f硬化指標之檢測方法 於是,本發明血管硬化指標之檢測方法,係利用一氣 囊對一受測者之肢體施壓來檢測動脈血管的硬化程度且 包含-加壓步驟、-洩壓步驟,及—計算步驟。又 在該加壓與沒壓步驟中,有兩種實施方式其一是將 環繞於該肢體之氣囊快速加壓至_高壓預設值以對該受 測者肢體之-進行施壓、然後將該氣囊逐步茂壓至一低壓 預設值’透過一儀器紀錄該氣囊在 轧震在逐步洩壓過程中之氣囊 内壓、6玄虱囊與動脈血管間交互作 化量,及相對應的時間,並#…引起之氣囊内壓變 子間並獲U動脈血f的舒張歷,收 縮壓,及平均動脈血壓;直_ &纟 ,、一疋先對%繞於該肢體之氣囊 201228634 逐步加壓至-南壓預設值,透過—儀器紀錄該氣囊在逐步 加壓過程中之氣囊内壓、該氣囊與動脈血管間交互作用所 引起之氣囊内壓變化量,及相對應的時間,並獲得該動脈 血管的舒張壓’收縮壓,及平均動脈灰壓,錢將該氣囊 快速洩壓至一低壓預設值,以結束對該受測者肢體之一所 進行的施壓。 於該計算步驟中,在該氣囊内壓相當於平均動脈血壓 的狀態下,推算動脈血管體積的變化量,且相對於平均動 脈血壓的血管硬化指標是以該收縮壓與舒張壓的差異值除 以動脈血管體積的變化量。 本發明之功效在於:不需要使用昂貴的儀器或是複 雜的量測及分析方式,只要獲得動脈血管的收縮壓、舒張 壓,以及動脈血管體積變化量,就能計算出相對於平均動 脈血壓時血管硬化的指標,不僅容易量測分析,也能降低 設備成本。 ^ 【實施方式】 有關本發明之前述及其他技術内容、特點與功效,在 以下配合參考圖式之一個較佳實施例的詳細說明中,將可 清楚的呈現。 參閱圖1與圖2,為本發明血管硬度量測方法之較佳實 施例,利用一氣囊1包覆在一受測者肢體2(上肢或下肢), 並充氣加壓該氣囊1 ’使其施壓於所包覆的肢體2部位,以 進行動脈血管21硬化程度的檢測,於本實施例中,是以量 測上臂之肱動脈為例說明,但不以此為限,該量測方法包 201228634 含-加壓步驟3、一攻壓步驟4,及—計算步驟5。 =切達到該力,步驟3及㈣步驟4 ,第一種 方式疋在έ玄加壓步驟3中,料IS2 u m厂 $對環繞於該肢體2的氣囊!進 ^速加❹一高㈣設值’然後在職壓步驟4中,對 ί肢體2、進行逐㈣壓,使該氣囊!逐步«至-低壓預 "值’透過—儀器紀錄該氣囊1在逐步㈣過程中該氣囊】 的内壓、該氣囊1與該動脈血管^間交互作用所引起之該Tlme), Impedance Plethysomgraphy, 201228634 Photo-Plethysmography, Oscillometry, Tonometry, and Analysis of Pressure Waveform. Among them, the ultrasonic technique can measure the flow rate of the it solution or the diameter of the blood vessel. If the blood pressure measurement at other locations is added, the arterial compliance can be derived, and a high resolution for the arterial atherosclerotic disease has been developed clinically. Intravascular Ultrasound System (IVUS), in pulse wave transit time analysis technology, using pulse wave velocity (PWV, Pulse Wave Velocity), vessel size (r) and wall thickness (h) The relationship, PWV2 = Eh / 2rp (where p is blood density), indirectly estimates the elastic coefficient of the arterial wall (7); other techniques such as impedance and optical plethysm utilize the electrical properties of the tissue and The difference in light absorbance at a specific wavelength is used to indirectly estimate the volume of the blood vessel, and then the blood pressure waveform is used to estimate the elastic force of the blood vessel; while the oscillation technique and the compression technique are respectively pushed through the fluid between the blood vessel and the balloon. Interaction and pressure measurement to estimate the compliance of the vessel wall; in the blood pressure waveform analysis technique, the index of the arterial blood pressure diastolic phase is utilized. The shape decay phenomenon is used to estimate the compliance of the vascular chamber. In addition, there is also a small area of indentation technique (Indentati〇n) to measure arterial compliance. For example, the inner valley disclosed in the Chinese Patent Publication No. 2〇〇91丨199 is used to gradually press the surface of the skin by an actuator. Concave, the average blood pressure of the skin is measured by a pressure sensor, and the depth of the depression at this time is sensed by a displacement sensor to obtain the average blood pressure and compliance of the artery. However, the above methods are quite complex and require a variety of sensing devices to cooperate with 201228634 as a 'adverse home or clinical application. Furthermore, the hardness of the arterial blood vessels is not a certain value, but varies with the blood pressure in the blood vessel lumen, that is, the hardness of the arterial blood vessel is a function of blood pressure and a function of time, and due to the mean arterial blood pressure (Mean Arterial Pressure, MAP) is the basis for the operation of various physiological functions. Therefore, the arterial atherosclerosis index at the mean arterial blood pressure not only has important physiological significance, but also has the most reference value. Therefore, how to easily obtain the average arterial blood pressure Arterial atherosclerosis refers to # ' is necessary. Although balloon sphygmomanometers containing reference indicators of blood vessel hardness have appeared on the market, the authenticity of their parameters and regional indicators are still questionable. SUMMARY OF THE INVENTION Therefore, an object of the present invention is to provide a method for detecting a blood f-hardening index under mean arterial blood pressure by using a simple method. Thus, the method for detecting an arteriosclerosis index of the present invention utilizes The balloon applies pressure to a subject's limb to detect the degree of hardening of the arterial vessel and includes a -pressurization step, a pressure relief step, and a calculation step. In the pressurizing and non-pressing steps, there are two embodiments. One is to quickly pressurize the airbag surrounding the limb to a high pressure preset value to apply pressure to the limb of the subject, and then The airbag is gradually pressed to a low pressure preset value. The internal pressure of the airbag during the gradual pressure relief, the interaction between the sacral sac and the arterial vessels, and the corresponding time are recorded through an instrument. And #... caused by the internal pressure of the balloon and the relaxation history of the U arterial blood f, systolic blood pressure, and mean arterial blood pressure; straight _ & 纟,, 疋 first to the airbag around the limb 201228634 gradually pressurized To the preset value of the south pressure, through the instrument to record the internal pressure of the airbag during the gradual pressurization, the change of the internal pressure of the airbag caused by the interaction between the airbag and the arterial blood vessel, and the corresponding time, and obtain The diastolic blood pressure of the arterial vasoconstriction, and the mean arterial ash pressure, the blood is quickly released to a low pressure preset value to end the application of pressure to one of the subject's limbs. In the calculation step, the amount of change in the volume of the arterial blood vessel is estimated in a state in which the internal pressure of the balloon is equivalent to the mean arterial blood pressure, and the index of the arteriosclerosis relative to the mean arterial blood pressure is divided by the difference between the systolic blood pressure and the diastolic blood pressure. The amount of change in the volume of the arterial vessel. The effect of the invention is that it does not require the use of expensive instruments or complicated measurement and analysis methods, as long as the systolic blood pressure, diastolic blood pressure, and arterial blood vessel volume change of the arteries are obtained, the relative arterial blood pressure can be calculated. The indicators of hardening of the arteries are not only easy to measure and analyze, but also reduce equipment costs. The above and other technical contents, features and effects of the present invention will be apparent from the following detailed description of the preferred embodiments. Referring to FIG. 1 and FIG. 2, a preferred embodiment of the method for measuring the hardness of a blood vessel according to the present invention is characterized in that an airbag 1 is used to cover a limb 2 (upper or lower limb) of a subject, and the balloon 1' is inflated and pressurized. Applying to the covered part 2 of the limb to detect the degree of hardening of the arterial blood vessel 21, in the present embodiment, the radial artery of the upper arm is measured as an example, but not limited thereto, the measuring method Package 201228634 contains - pressurization step 3, a tapping step 4, and - calculation step 5. = cut to the force, step 3 and (4) step 4, the first way is in the έ 加压 pressurization step 3, the material IS2 u m factory $ for the airbag surrounding the limb 2! The speed is increased by a high (four) setting value. Then in the occupational pressure step 4, the limb 2 is pressed (four) to make the airbag! Step by step «to - low pressure pre-quote value" through the instrument to record the internal pressure of the balloon 1 during the step (four) process, the interaction between the balloon 1 and the artery and the artery
« 1的内壓變化量,及相對應的時間,並獲得該動脈血 官21的舒張壓,收縮壓,及平均動脈血壓。 第-種方式是在該加壓步驟3中,對環繞於該肢體2 的氣囊1進行逐步加壓至一高壓預設值,透過一儀器紀錄 該氣囊1在逐步加壓過程中該氣囊1的内壓、該氣囊!與 «玄動脈血s 21間交互作用所引起之該氣囊1的内壓變化量 ’及相對應的時間’並獲得該動脈血f 21 &舒張壓,收縮 壓,及平均動脈血壓,然後在該洩壓步驟4中,對該肢體2 進行快速洩壓,使該氣囊1快速洩壓至一低壓預設值。 於本實施例中,該高壓預設值通常是高於一般人的收 縮壓,其最佳範圍為! 〇〇〜2〇〇毫米汞柱,該低壓預設值通 常是低於一般人的舒張壓,其最佳範圍為20〜60毫米汞柱 ’在兩種加壓與洩壓方式中’其一是當該氣囊1快速加壓 至該高壓預設值後,會以每秒3·5毫米汞柱的速度對該氣囊 1進行逐步洩壓,其二是當該氣囊丨以每秒3_5毫米汞柱的 速度逐步加壓至該高壓預設值後’再對該氣囊1進行快速 汽壓’而該儀器為電子血壓計,由於該儀器之結構,及加 201228634 壓與/曳麼的方法為熟知該項技藝者所能輕易理解,不再予 以繪示及贅述。 該動脈血管21的硬度E(或稱為抗彈性力)定義為血管 壓力的變化量(ΔΡ)與血管體積的變化量(Δν)之比例,如式 (1)所示: ^ ΑΡ Ε =- ............................................................ 如圖1所示,將一寬度為L的氣囊丨環繞於該肢體2, 該氣囊1加壓時,該氣囊1的内壓與體積之間是成一非線 性的關係,但是如圖3所示,當該氣囊丨的内壓維持在平 均動脈血壓時’且當其内壓變動或振盪極小時,則很明顯 地在此狹窄範圍内的氣囊内壓與體積之間的關係,可視為 是近似線性的。 參閱圖1及圖3,該動脈血管21中的血液和介於該動 脈血管21及氣囊1之間的介質組織22與骨頭23是屬於較 不可壓縮(Incompressable)的物質’而該氣囊i中的空氣是 屬於很容易被壓縮(Compressable)的物質。當氣囊内壓處在 平均動脈血壓時,由於該氣囊1和動脈血管21之間的交互 作用,如圖3所示’該動脈血管21的體積在心臟舒張期最 小點(A)和心臟收縮期最大點(B)時所產生的體積變化量(即 △ Va=Va,sys—Va,dia),會直接反映在該氣囊1的體積變化 量(△VfVc’l —Ve,2)上’也就是該氣囊!的體積最大點(C) 應該要相對於該動脈血管21的體積最小點(A),而該氣囊1 的體積最小點(D)應該要相對於該動脈血管21的體積最大點 201228634 (B) ’故該動脈血管21有一定比例的體積變化量會反映在該 氣囊1的體積變化量上。 如圖4所示’於本實施例中,是利用壓振技術 (Oscillometry)來測出受測者的收縮壓(ps)、舒張壓(pd)、心 率及平均動脈血壓(Meail Arterial Pressure,MAP),其中受測 者的平均動脈血壓相對於在逐步洩壓或逐步加壓過程中氣 囊内壓脈動振幅(ΔΡ。)達到最大(ΔΡ(; ma〇時的氣囊内壓d)。« 1 internal pressure change, and the corresponding time, and obtain the diastolic blood pressure, systolic blood pressure, and mean arterial blood pressure of the arterial blood. The first mode is that in the pressurizing step 3, the airbag 1 surrounding the limb 2 is gradually pressurized to a high pressure preset value, and the airbag 1 is recorded by an instrument during the stepwise pressurization process. Internal pressure, the airbag! And the amount of change in the internal pressure of the balloon 1 caused by the interaction between the x-arterial blood s 21 and the corresponding time 'and obtain the arterial blood f 21 & diastolic blood pressure, systolic blood pressure, and mean arterial blood pressure, and then In the pressure step 4, the limb 2 is quickly relieved, so that the airbag 1 is quickly released to a low pressure preset value. In this embodiment, the high pressure preset value is usually higher than the average person's shrinkage pressure, and the optimal range is! 〇〇~2〇〇mmHg, the low pressure preset value is usually lower than the average person's diastolic pressure, and its optimal range is 20~60mmHg 'in both pressurization and pressure relief modes' When the airbag 1 is rapidly pressurized to the high pressure preset value, the airbag 1 is gradually relieved at a speed of 3.5 mmHg per second, and the second is when the airbag is 33_5 mmHg per second. The speed is gradually pressurized to the high pressure preset value, and then the balloon 1 is rapidly vaporized. The instrument is an electronic sphygmomanometer. Due to the structure of the instrument, and the method of adding 201228634 pressure and/or drag is known. Can be easily understood by the artist and will not be shown or described. The hardness E (or called elastic resistance) of the arterial blood vessel 21 is defined as the ratio of the amount of change in blood vessel pressure (ΔΡ) to the amount of change in blood vessel volume (Δν) as shown in the formula (1): ^ ΑΡ Ε =- .................................................. .......... As shown in Fig. 1, a balloon 宽度 having a width L is wrapped around the limb 2, and when the balloon 1 is pressurized, the internal pressure and volume of the balloon 1 are non-linear. a linear relationship, but as shown in Fig. 3, when the internal pressure of the balloon is maintained at the mean arterial blood pressure 'and when the internal pressure changes or the oscillation is extremely small, it is apparent that the internal pressure of the balloon is within the narrow range The relationship between volumes can be considered to be approximately linear. Referring to Figures 1 and 3, the blood in the arterial vessel 21 and the media tissue 22 and the bone 23 interposed between the arterial vessel 21 and the balloon 1 are substances that are relatively incompressible and in the balloon i Air is a substance that is easily compressible. When the internal pressure of the balloon is at the mean arterial blood pressure, due to the interaction between the balloon 1 and the artery 21, as shown in Fig. 3, the volume of the artery 21 is at the minimum point of diastole (A) and systole. The volume change amount (ie, ΔVa=Va, sys_Va, dia) generated at the maximum point (B) is directly reflected in the volume change amount (ΔVfVc'l - Ve, 2) of the airbag 1 ' It is the airbag! The maximum volume point (C) should be relative to the smallest point (A) of the volume of the arterial vessel 21, and the smallest volume point (D) of the balloon 1 should be relative to the volume of the artery 21 at the maximum point 201228634 (B) Therefore, a certain proportion of the volume change of the arterial blood vessel 21 is reflected in the volume change amount of the air bag 1. As shown in Fig. 4, in this embodiment, the systolic blood pressure (ps), diastolic blood pressure (pd), heart rate, and mean arterial blood pressure (Meail Arterial Pressure, MAP) of the subject are measured by Oscillometry. The average arterial blood pressure of the subject is maximized relative to the intrapulmonary pressure pulsation amplitude (ΔΡ.) during gradual pressure relief or stepwise pressurization (ΔΡ (; airbag internal pressure d at ma〇).
於该計算步驟5中,能計算獲得血壓量測過程中的動 脈血管21體積變化量(△%),而在該動脈血管21的壓力等 於平均動脈血壓的狀態下,該動脈血管21的硬化指標 (emap)是以收縮壓(Ps)與舒張壓(Pd)的差異值除以該動脈血管 21的體積變化量(Λν^Αρ),如式(2)所示:In the calculation step 5, the volume change (Δ%) of the arterial blood vessel 21 during the blood pressure measurement can be calculated, and the hardening index of the arterial blood vessel 21 is obtained in a state where the pressure of the arterial blood vessel 21 is equal to the average arterial blood pressure. (emap) is the difference between the systolic blood pressure (Ps) and the diastolic blood pressure (Pd) divided by the volume change of the arterial blood vessel 21 (Λν^Αρ), as shown in the formula (2):
當氣囊内壓維持在平均動脈血壓時,因血流脈衝所導 致的氣囊内壓脈動振幅僅約卜3冑米汞柱,所以在此狹窄 範圍的氣囊内壓變動,在常溫下該氣囊内壓⑹和氣囊體積 (vc)之乘積可視為一常數,也就是Ρεχ、=常數,同時,在此 1〜3毫米汞柱的狹窄變動範圍内, 可視為一固定值,如式(3)所示: 該氣囊1的硬度(Ec,map)When the internal pressure of the balloon is maintained at the mean arterial blood pressure, the amplitude of the pulsation of the internal pressure of the balloon caused by the blood flow pulse is only about 3 mm of mercury, so the internal pressure of the balloon in this narrow range fluctuates, and the internal pressure of the balloon is normal at normal temperature. (6) The product of the airbag volume (vc) can be regarded as a constant, that is, Ρεχ, = constant, and at the same time, within the narrow variation range of 1 to 3 mmHg, it can be regarded as a fixed value, as shown in formula (3). : The hardness of the airbag 1 (Ec, map)
Ec MAP —Ec MAP —
^C,MAP ^C,MAP^C, MAP ^C, MAP
PC=MAP (3) 其中,如圖3所示 △VC,MAP和ΔΡ^μαρ分別為氣囊内壓 201228634 維持在平均動脈血壓時,該氣囊1體積變化量的振幅及該 氣囊内壓變化量的振幅,也就是Δν(;,ΜΑΡ=νΜ_νΜ及 APc,map=Pc,i- Pc,2,因此: Λ F _ ^CMAP C,MAP----PC=MAP (3) wherein, as shown in Fig. 3, ΔVC, MAP and ΔΡ^μαρ are the amplitudes of the volume change of the balloon 1 and the amount of change in the internal pressure of the balloon when the intravesical pressure 201228634 is maintained at the mean arterial blood pressure, respectively. The amplitude, that is, Δν(;, ΜΑΡ=νΜ_νΜ and APc, map=Pc,i-Pc,2, therefore: Λ F _ ^CMAP C, MAP----
Ec'mP Pe=MAP...................................... 如前所述,當氣囊内壓維持在平均動脈血壓時,該氣 囊1的體積變化量會反應一部分該動脈血管21的體積變化 量,因此該動脈血管21的體積變化量等於該氣囊丨的體積 變化量除以一常數(k),因此 〜Va,MAP=jXAVc,mp ±χ^£ΜΑΡ_ k ec map (5)Ec'mP Pe=MAP..................................... As mentioned earlier, when When the internal pressure of the balloon is maintained at the mean arterial blood pressure, the volume change of the balloon 1 reflects a part of the volume change of the artery 21, so the volume change of the artery 21 is equal to the volume change of the balloon 除 divided by a constant. (k), therefore ~Va, MAP=jXAVc, mp ±χ^£ΜΑΡ_ k ec map (5)
--MAP 由於該動脈血管21的體積變化量的一部份會反應至該 氣囊1的體積變化量,因此該常數k介於〇和丨之間,並 將方程式(5)代入方程式(2),則:-MAP Since a part of the volume change of the arterial blood vessel 21 is reflected to the volume change of the balloon 1, the constant k is between 〇 and 丨, and equation (5) is substituted into equation (2) ,then:
k Ec,MApk Ec,MAp
Pc =MAPPc = MAP
經整理後,可得到:After finishing, you can get:
PP APC,PP APC,
MAP ⑺MAP (7)
--MAP 其中,PP為脈壓(Pulse Pressure),等於收縮壓(卩5)減掉 舒張壓(Pd),Ee,MAP為該氣囊1在平均動脈血壓時的硬度, 而當氣囊内壓維持在平均動脈血壓時,該氣囊1的硬度又 10 201228634 可視為定值(也就是常數),因此,只要能獲得該動脈血管 之收縮壓與舒張壓的差異值(PP),以及該氣囊】在相對於該 動脈血管21的收縮壓與舒張壓之間的氣囊内壓差異值 (△PC,MAP) ’就能利用式(7)來測得在平均動脈血壓時的血管 硬化指標(EjvjAP)。 透過上述實施方式的說明,本發明血管硬化指標之檢 測方法,只要能獲得該動脈血管21之收縮壓與舒張壓的差 異值(PP)、該氣囊1在相對於該動脈血管21的收縮壓與舒 張壓之間的氣囊内壓差異值(ΔΡε,ΜΑρ),以及該氣囊i在平均 動脈血壓時已知的硬度(Ee,MAp),就能獲得該動脈血管21的 硬化指標,而有助於了解該動脈血管21之彈性變化,不需 使用昂貝的儀器或是複雜的分析演算方法,故確實能達成 本發明之目的。 惟以上所述者,僅為本發明之較佳實施例而已,當不 月b以此限定本發明實施之範圍,即大凡依本發明申請專利 範圍及發明說明内容所作之簡單的等效變化與修飾,皆仍 屬本發明專利涵蓋之範圍内。 【圖式簡單說明】 圖1是一剖面示意圖,說明本發明血管硬化指標之檢 測方法的較佳實施例中,氣囊環繞於一肢體時的剖面情形 > 圖2是一量測流程圖,說明該較佳實施例之量測分析 步驟; 圖3是一不意圖,說明氣囊與動脈血管之交互作用; 201228634 及 圖4是一氣囊内壓變動圖,說明振盪式血壓量測過程 中氣囊内壓變動的情形。--MAP where PP is Pulse Pressure, equal to systolic blood pressure (卩5) minus diastolic blood pressure (Pd), Ee, MAP is the hardness of the balloon 1 at mean arterial blood pressure, and when the balloon internal pressure is maintained At the mean arterial blood pressure, the hardness of the balloon 1 is again 10 201228634 can be regarded as a fixed value (that is, a constant), therefore, as long as the difference between the systolic blood pressure and the diastolic blood pressure (PP) of the arterial blood vessel can be obtained, and the airbag is The value of the intravascular pressure difference (ΔPC, MAP) between the systolic blood pressure and the diastolic blood pressure of the arterial blood vessel 21 can be measured by the equation (7) to determine the arteriosclerosis index (EjvjAP) at the mean arterial blood pressure. According to the description of the above embodiment, the method for detecting an arteriosclerosis index of the present invention is such that a difference value (PP) between the systolic blood pressure and the diastolic blood pressure of the arterial blood vessel 21 and a systolic blood pressure of the air bag 1 with respect to the arterial blood vessel 21 are obtained. The difference in the internal pressure of the balloon between the diastolic blood pressures (ΔΡε, ΜΑρ) and the known hardness (Ee, MAp) of the balloon i at the mean arterial blood pressure can obtain the hardening index of the arterial blood vessel 21, and contribute to Knowing the elastic change of the arterial blood vessel 21 does not require the use of an Amber's instrument or a complicated analytical calculation method, so that the object of the present invention can be achieved. However, the foregoing is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention, that is, the simple equivalent changes made by the scope of the invention and the description of the invention. Modifications are still within the scope of the invention. BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a schematic cross-sectional view showing a cross-sectional view of a balloon in a preferred embodiment of a method for detecting an arteriosclerosis index according to the present invention. FIG. 2 is a flow chart showing the measurement. Figure 3 is a schematic diagram illustrating the interaction between the balloon and the arterial vessel; 201228634 and Figure 4 are a variation of the internal pressure of the balloon, illustrating the internal pressure of the balloon during the oscillating blood pressure measurement process. The situation of change.
12 201228634 【主要元件符號說明】 1 氣囊 23 骨頭 2 肢體 3 加壓步驟 21 動脈血管 4 洩壓步驟 22 介質組織 5 計算步驟12 201228634 [Explanation of main component symbols] 1 Airbag 23 Bone 2 Limb 3 Pressurization step 21 Arterial blood pressure 4 Pressure relief step 22 Media organization 5 Calculation steps
1313
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