TW200819112A - noninvasive method to evaluate the new normalized arterial stiffness - Google Patents

Abstract

The present invention discloses a noninvasive method to evaluate the new normalized arterial stiffness from its longitudinal scanning and the real time blood pressure during cardiac cycles. Both the normalized arterial stiffness and intima-media thickness are capable of determining by the present invention, which comprises the fast arterial strain detection and the statistical application. Because of the high Repeatability and Reproducibility, the present invention is suitable for screening the coronary artery disease (CAD) or the disorder of metabolism.

Description

200819112 IX. DESCRIPTION OF THE INVENTION: TECHNICAL FIELD The present invention relates to a method for detecting the hardness of a non-invasive vascular material. A non-invasive method that is safe, fast, and reproducible, dynamically detecting human arterial, intima-media thickness and stiffness. [Prior Art] The most direct and extensive arterial stiffness indexes at present are Pulsed Wave Velocity (PWV), incremental stiffness (incremental StlffneSS) and hardness (stiffness /5), when the overall compliance of the artery (Compliance) When it is reduced, pwv will increase, and the hardness and hardness will increase. PWV is easy to measure and inexpensive, but there are many assumptions for measurement, and it is not possible to perform hardening evaluation for specific arteries. Incremental hardness and hardness must be achieved through expensive non-invasive instruments (such as ultrasound systems). The deformation is very subtle, so the pros and cons of measurement technology become the key. In addition, some researchers have suggested that the incremental hardness and hardness/3 used for f cannot reflect the hardening of the arterial material. Using continuous arterial longitudinal imaging device to measure the deformation of arteries by blood pressure, it is the easiest way to estimate blood vessel hardness indirectly according to Hooks Law, but there are still many problems that are difficult to solve. The first is how to correctly track the deformation of blood vessels. How to deny the arterial stiffness with viscoelastic properties, the most widely measured method for vascular deformation is the use of echo phase tracking (Phase Treking), for example: 5 200819112

RF of Hokes (Ultrasound Med & Biol. 1 9 8 5; 11: 51-59)

Cross Correlation, or Kanai et al. (IEEE Trans. On Ultrasonics, Ferroelectrics, And Frequency Control, 1 99 6 ; 43 : 79 1 _ 8 1 0) , Hasegawa and Kanai ( IEEE

Transactions on Ultrasonics, Ferroelectrics, and

Frequency Control, 2004; 5 1 (1): 93 - 1 08) Proposed phase tracking with cost function optimization, in addition to Rabben et al. (UlUasound • Med· & Bi〇l· 2002; 28(4): 5 07- 5 1 7) Specially consider the phase tracking of the Doppler shift correction of the echo to increase the accuracy of the tool. There are also Echo Tracking, such as s h au, Y. W (Ultrasound Med & Biol. 1 9 9 9 ; 2 5 (9): 1 3 7 7 - 8 8 ). For obvious deformations such as the common head artery (CCA) of the human body, experience has taught us that the arterial circumference is subjected to the binding of the coated muscle to cause great variation in measurement. For this reason, the present invention proposes a method for detecting the hardness of a non-invasive vascular material. It has a simple, _ repeat H and 4 inch, and in order to match this detection technology, the present invention simultaneously develops an arterial edge chasing technology. The fork is limited to measurement techniques and complex arterial stiffness can only be expressed as an indicator. Correct

The arteries are regarded as independent elastic materials during the expansion process and the relaxation process. Its Weng Xue 饯 S Α Π B U _ vertical elastic material

In the tensile test, the rising curve of the swelling process approximates the exp function, so it is defined that the hardness of 200819112 is not. If this phenomenon is ignored, the simpler incremental hardness can be used. ^

The use of incremental hardness or hardness stone can be itchy B to estimate the trend of blood hardness. 'Because these two indicators are not for the thickness of the blood vessels - 仃払 quasi-chemical, so it is not the true hardness of the artery, Unless the arterial & 7 ratio of each subject is not significantly different from the official diameter, the mechanical properties of the vascular material f can be correctly reflected.

The physical mechanism of global arteriosclerosis mainly comes from the thickening of the arterial wall or the hardening of the material. Tanifaki et al. (Athe_eie_is coffee ww) study pointed out that in the second stage of diabetes patients, the femoral artery blood vessel hardness and intima-media The thickness is positively correlated, van P Ning lee. 2 0 0 1 ; 3 2 : 4 5 4 ) Indirect measurement of arterial stiffness from PWV is significantly associated with the intima-media thickness of the blood striatum (Inti trace Media (5), please) , scuteri (Cardiology, 2004; 43(8) 1 3 88 1 395) from the long-term study of 々η名 测者, using the ultrasonic two-dimensional gray-scale image to analyze the intima-media thickness and blood vessels of the right cephalic artery The deformation, their research shows that if there are metabolic related diseases, such as high blood pressure, obesity, etc., the blood vessel hardness has a significant increase trend, Jan (Ultras () und in Med. & Biol.,

Vq1· 30' Ν〇· 2, ρρ· 1 47-1 54, 2004 ) Using the 2-D ultrasonic measurement of the circular cut area of CCA, the study proposes a first-order linear relationship between the age and the hardness index of cca (R =〇76), and from past research experience, it is pointed out that Cca's hardness index will increase with age. If there is metabolic or cardiovascular disease, the arterial stiffness and neck IMT are obviously enlarged, Angelo Scuteri 200819112 (American College 〇f Cardiology V〇L 43? No. 8? 2 0 04) Measure the pwv between the neck and the stock (carotid an (j fem〇rai) and (2c; a IMT mentioned in the new 卩Patients with abnormal metabolism in the east suggest that IMT and hardness should not be considered as two different independent indicators. In addition, Shi 200 1; 38:1181) After long-term observation of patients with hypertension, the aorta was proposed. Hardness is an independent indicator of coronary artery disease. Although arterial stiffness can reflect the compliance of vascular materials, these changes must be made by the elasticity of changes in blood structure, especially the relationship between vascular hardness and atherosclerosis. Mechanics to answer, The overall arteriosclerosis is caused by the hardening of the material itself or the thickening of the arterial wall, which is in the past, the incremental hardness or the hardness of 5 can not be answered. [Invention] In view of the lack of the prior art, the object of the present invention is The invention provides a non-invasive method for detecting the hardness of a vascular material, and dynamically detects the arterial stiffness and the intima-media thickness of the human body in a safe, fast-calculating and highly reproducible non-invasive method. The present invention utilizes a two-dimensional continuous artery longitudinal The imaging device (taking 2D ultrasound as an example) and the continuous arterial blood pressure signal acquisition device, through the rapid arterial image edge extraction technology and statistical principle, obtain the intima-media thickness and hardness of the living artery, and the measurement results are very high. Good reproducibility can be applied to the detection of cardiovascular related diseases and metabolic abnormalities and the efficacy of drugs. In particular, the arterial hardness of arterial thickness correction proposed in 200819112 can directly reflect the hardening of arterial wall material. Purpose, the present invention provides a method for detecting the hardness of a non-invasive vascular material, The steps include: (a) measuring the systolic and diastolic blood pressure of the arm blood vessel to replace the blood pressure of the total carotid artery (CCA); (b) the arterial longitudinal imaging device and the computer analysis platform, and measuring the total body with appropriate contact force Carotid artery, or other artery to be measured; (c) Display a two-dimensional image of the arterial diameter of the blood vessel on the screen, and adjust the direction of the arterial image to provide an image of the longitudinal section of the artery; (4) Confirm the correctness of the image of the longitudinal section of the artery, Determining that the ultrasonic wave actually sweeps the center of the eye to the maximum diameter of the artery; (4) transmits the longitudinal longitudinal image of several heartbeat cycles to the computer platform; (f) (four) the true scale of the scale-converted image pixel of the longitudinal image of the pulse (g) According to the arterial sputum hardness gradient, the maximal m-first image of the artery (10) and the edge of the adventitia; (8) processing the continuous arterial diameter data, calculate the arterial intima-media thickness map (IMT) And the time-varying curve of the arterial diameter; and (1) the new parameters for estimating the optimal IMT and calculating the arterial stiffness by statistical principle. In some embodiments, the method for detecting the hardness of the non-invasive vascular material of the present invention, the surgical cut (4) of the towel (4) (b) includes a suitable contact force, wherein the contact force should be less than the diastolic pressure. In certain embodiments, the method for detecting the hardness of a non-invasive blood material of the present invention, wherein the longitudinal section of the artery of step (4) must comprise an adventitia of the artery (field plus (4) 200819112 and intima/media (Intima_Media;). The invention discloses a method for detecting the hardness of a non-invasive vascular material, further comprising an -arterial image edge method, wherein the faStphasetracking technique and the echo tracking (ech〇track_) correction are performed on the image edge; wherein the artery image The edge method is based on image gradient or intensity data for discrete Fourier transform (DFT), taking several low-frequency phase angle differences, and extracting the actual position of the arterial wall via echo correction under fast phase chasing.

shift. The method for detecting the hardness of a non-invasive vascular material according to the present invention further comprises temporal movement of the longitudinal section area of the artery image, and uses the change in area to estimate the deformation of the artery. The non-invasive endocardial _ intermediate layer thickness quantification method of the present invention uses a large number of consecutive images or data for statistical evaluation, taking into account the average thickness under the entire heart and hop period. The preferred embodiment of this month, in which the arterial stiffness ((10) heart! sUffness) must be combined with the Young's coefficient, including _ΙΜτ instead of the overall arterial wall thickness to calculate the arterial stiffness. The method for detecting the hardness of non-invasive vascular materials, wherein the thickness of ΙΜτ can be used to calculate the hardness of the material of the layer, including the Young's modulus (Y_g s Modulus) and the shear modulus (shear M〇) Dulus). [Embodiment] 200819112 The figure is a sound diagram of the non-invasive blood vessel hardness detecting method of the present invention. In which the blood pressure of the human common carotid artery (CCA) cannot be measured, and the systolic blood pressure and diastolic blood pressure of the arm blood vessel are measured instead. 6. Provide ultrasonic probe 4 (linear probe is the best) and computer analysis platform Μ; and measure the total carotid artery (CCA) 2 with appropriate contact force (less than diastolic pressure), or other arteries to be measured (recommended arterial diameter) More than 0.2mm or more). The bloody artery diameter pulsation 2D image (B_m〇de) is displayed on the screen, and the scanning direction of the ultrasonic probe is adjusted to be the longitudinal section of the artery. The length of the longitudinal section may vary depending on the scanning range of the probe (the length is at least 1 cm or more). ). To confirm the correctness of the longitudinal longitudinal image 8, the longitudinal section of several centimeters must contain the intima and adventitia of the superior and inferior margins to determine that the ultrasound actually scans to the center of the largest diameter of the artery. The arterial longitudinal image 8 of several heartbeat cycles is transmitted to the computer platform 16 via the interface 丨2, and the image frame rate (FrameRate) is at least (10) or more. The arterial stiffness analysis software 18 is used to convert the image pixels from the scale of the ultrasonic scanned image. The true scale scale 'sets the edge threshold of the intima and adventitia of the initial 35 (first image), treats the continuous arterial diameter data, calculates the intima-medla thickness of the arterial intima-medla thlckness; IMT), and the arteries The time curve of the pipe diameter. Finally, the optimal IMT and new parameters for calculating arterial stiffness are estimated by statistical principles. 200819112 Example 1: Improvement of arterial measurement method The most common way to measure vascular pulsation is to use the time axis as the reference, perform M-Mode of echo tracking according to the same position, or use a more complicated 2-D image to perform arterial circle. The deformation of the cut-off area is used as the basis for the calculation of arterial stiffness. Unfortunately, they all vary greatly with the position of the arteries. For this reason, we use the arterial area of the longitudinal section of the artery to make some measurement adjustments. section. Since the intima-media must be clearly visible in the state of vertical incidence of ultrasound, in order to confirm that the longitudinal scanning plane of the image is the largest artery diameter, the longitudinal section must contain the intima-media of the blood vessel. (inuma - media) can ensure that the scan passes through the center of the artery, and this is an important basis for assessing the correctness of image capture, as shown in Figure A below. In general, the ultrasonic probe and the scanning depth can cover the length of the blood vessel by about several cm'. Therefore, unlike the measurement of the arterial sectional area of Μ_Μ_ or 2D, the resolution of the arterial strain is significantly increased with the length of the slit. The improvement in strain resolution is the data obtained by measurement completely as shown in the second _. Usually, the deformation of the arterial motion has only a few image points (pixeIs). To do this, numerical interpolation is used to increase the resolution. As shown in Figure C, the numerical interpolation form does not increase the correctness of the measurement. Through the k-axis Y-direction (vertical axis) broom echo intensity (image brightness), the local gradient of the arterial wall is the maximum value of the maximum and the maximum value is taken along the X-axis (horizontal fast edge tracking) Ping, seven 'rare by J Jinyu / 丨 test the second example of the description) and coloring, the same principle will be used to detect the outer membrane of the tough membrane for the internal amine flat, 1 』 bamboo 劂 劂 Μ detection, can At the same time, the area of the picking area defines it 200819112 IMT and the strain of the vein (10) is called, as shown in the third figure. As shown in the first figure, at a certain time t, the central axis length of the longitudinal section of the artery is Lc(1), and the longitudinal section of the artery is cut. Area (excluding the underlying intima), the longitudinal section of the artery (including the underlying intima) Ao (1), the smallest area of the longitudinal section of the artery (including the underlying intima) Amin ° The average bureaucratic _· Di_r(t) = Ai(t / Lc(1) outer (t)=Ao(t) / Lc(t) The average mT is calculated as follows: (1)=m(1); the strain of the artery is calculated as follows: strain(1)=A. (1)/Amu 0 After the above analysis, the ΙΜΤ distribution map can be output. For example, as shown in the fourth figure, as shown in the fourth figure, as the arteries are healthy or not, as shown in the fourth figure. Estimate, especially the hardness of the ankle and arteries, wherein the fourth figure A is the 1MT distribution map, the more concentrated the distribution of the bar graph represents the more positive the measurement ^ the fourth figure $ is: the relationship between the longitudinal section of the pulse and the time, in no Numerical interpolation, also has a high-resolution waveform. Comparison of renaturation correct arterial representation

Can increase the resolution? /3 200819112 Example 2: Intra-arterial-media thickness (IMT) calculation method improvement 2D arterial sectional area measurement analysis (4) is better, even the thickness variation of diastolic and I can be measured Although the waveform of bribes changing with time is not very smooth, there is a significant negative correlation (r=_G~ in systolic blood pressure, thinner, diastolic, and thicker, as shown in Figure A,

The change of k kinds of IMT is impossible in the past M〇ti〇n_M〇de phase tracking (10)_trackmg), as shown in the fifth figure B, wherein the fifth figure a is the centimeter CCA slitting area operation to resolve the arterial diameter In inverse proportion, the other fifth picture B is a one-dimensional image analysis, Xie and blood pressure or arterial diameter is completely undetectable. The figure can clearly detect IMT and blood pressure or

Motion-Mode operation quantity 0 Traditional IMT # calculation is to use the longitudinal section of the artery for echo tracking (Ech〇 true king) $疋 phase chasing (ph prison (four) to extract the endarterial artery

=Boundary 'and enter ^ to calculate the thickness, echo tracking in the arterial wall image quality is poor, : breakpoints or breakpoints occur, resulting in failure to trace, although the use of phase tracking is less ^ the above problem 'but the phase tracking The result is unreasonable. For this reason, the present invention uses the echo of the Dali to trace the continuous image, obtains the Xie distribution, and estimates the normal τλΛΤ - ' from the condition of the normal distribution. Thus, not only can the interference under special conditions be avoided, J female Factors such as breathing and shaking of the tester will also increase the accuracy of the measurement. Arterial wall motion detection

Phase Tracking) is the most widely used measurement technology. It is used in one dimension of 200819112

Motion-Mode images are feasible and stable, but they are completely inappropriate in two-dimensional slit images, and they are often misused in IMT measurements. Since the longitudinal arterial image is an independent image measured by multiple ultrasound probes, phase tracking is based on the similar properties of the arterial wall to estimate the possible motion of the arterial wall. If the condition of similarity is used, each pen is lost. The independence of the measurement. The invention improves the traditional phase tracking and accelerates its operation, which is called Fast Phase Tracking as a preliminary rough estimation of arterial wall motion, and then is corrected by echo tracking (Ech0 Tracing), so the method has The traditional phase tracking and the improved speed, as well as the independence of measurement, etc., as shown in the sixth figure. In the sixth picture A, the maximum Echo gradient is obtained, and the coordinates γ〇 and echo intensity b〇 are obtained as reference bases for all arterial ridges. The sixth figure B is fast phase tracking (FastphaseT(10)(d), from Υ〇 Obtain L-length data for DFT operation, in which only the phase difference Δφ of low frequency ^ 2 Hz) is obtained, and the initial arterial edge extraction port f) is performed, and the sixth figure c is the echo intensity tracking revision (Ech〇丁^咖吨Correction), searching for the same B〇 position from Yi near the edge of the artery w w. Example 3: Improvement of arterial stiffness calculation method Now that there is a physical model, the remaining work is how to define the stress and strain of the artery. The definition of arterial strain is h = (D_D.)/D. , D. It is the original diameter of the artery without any external pressure. Because the artery is a multi-layer non-isotropic material, there is internal stress in the P itself, and the original tube diameter cannot be obtained in the living experiment.

1S 200819112 This traditional strain is the simplest ε = ε = ( D - Dsys) / Dsys, Dsys is the arterial diameter of the contraction period. Under the ultrasound image, the arteries contain intima and media and adventitia and muscles and fat outside the arteries. Because intima is only a thin layer of cells, ultrasound is undetectable, but Media is rich in coUagen, which results in higher hardness, especially in the imaging of the common carotid artery. As for the outer membrane, it is a soft tissue, and the thickness is about 1/3~1/2 of the claw. If it is hypothetical Everyone has a small Dsys/t gap. The commonly used Incremental stiffness and stiffness 表示 are expressed as follows: Incremental Stiffness = S sys - ε dia stiffness β = 4^^) One ^ (匕.) S sya - S dia PSyS and Pdia, respectively, are sphygmomanometer and diastolic waste measured by an air bag sphygmomanometer. ^ • ^ The nucleus of the vein causes uneven internal stress distribution, blood pressure inside the artery and pressure on the lateral tissue of the artery It is difficult to measure correctly in the living state without interference: 'So the actual line of arterial stress is really difficult, if the artery is simplified into a thin homogeneous material, and the lateral tissue of the artery is ignored. The effect, the definition of stress P is very easy, so the theoretical calculation of the hardness of the arteries is as follows: 200819112 ^sys ^ ^dia t

Dsys ^sys £dia ' It is a pity that because the adventitia and surrounding tissue are difficult to distinguish correctly under ultrasound images, it is difficult to calculate correctly because of the correct physical theory, but according to the in vitro biomedical materials of Fimg In the extension experiment, it was confirmed that the hardness of the intima of the artery is about 5 to 丨〇 times that of the outer membrane. Therefore, we can reasonably improve the arterial stiffness φ. The improved arterial stiffness calculation method can highlight the arterial material. The change, in addition to this, is more in line with the theory of thin tube hardness calculation of material mechanics. This paradox can be confirmed in our clinical tests. ' μ ^ _ ^sys - Pdia Dsyjs Ssys-^dlQ IMT E Jn(Psys)-HPdia) DSys

β €sys ' ^dia IMT Figure 5A shows that due to the improvement of measurement technology, it can be found that imt Lu is compressed at systolic pressure. The maximum time for IMT to be compressed occurs earlier than the highest blood pressure, which is the result of fluid shear stress on the blood vessel wall. Through the theory of elastic mechanics, the Young's modulus (Y〇img, s Modulus) and the shear modulus (M〇dulus) of IMT can be calculated by blood pressure, IMT deformation and At. EXPERIMENTAL RESULTS 1 • The longitudinal section of the artery has a higher measurement repeatability than the section of the section. The 2-D CCA section is compared with the analysis of the longitudinal section used in this paper. At similar time, the suppression is used! _111) 15000 5~i2mh°z 200819112 Linear probe measurement CCA 2 "μ2a by the door one... θ 2 seven-cut and longitudinal sections each ten times, the scanning depth is fixed at 4.8cm, using super The sound compensation setting of the 5th and 15th fmeS is downloaded through the network as the uncompressed d coffee format. (4) End points: After each measurement, the probe must leave. The surface of the skin, and then - the person according to the other general position to carry out the next _ &: the target, the results of the test, ten times, showing that the result of using the cut surface is slightly higher than the longitudinal section of the tube back ^ # Blood hardness index. However, the analysis results of the longitudinal section are better (CV = 1 〇〇 / 〇), 5 is later 〇; the analysis results of the traditional circular cut surface are significantly unstable (CV = 19%), ▲ 曰 ^ ^ 19 /. Therefore, we believe that the longitudinal section is measured in a more repeatable manner. 2. Whether different operators will result in different analysis results: Solicitation of CM 自愿 voluntarily and without any cardiovascular disease, the CM is hard, the test is repetitive, and the voluntary test is measured twice. Over the week, each measurement analysis was collected by two operators independently, and the statistical results after the measurement were found. 'Although different operators have slightly different results, there is no statistical difference (!>< 0·0_), the measurement results between the two are highly positively correlated, and the results of the calculation of intra reIiabimy are selected 6 times (4) ~22% are 12.8%. ^

Member Mean Stiffness β KP "~ A 0.067 Mpa 0.955 -—--- ———. <0.0001 _ B ------ 0.074 Mpa ———————— In order to reduce the measurement error Finally, we tested the CCA hardness index for DM-(n=8) and a small number of CAD patients (n=7), and we also measured the normal subjects without this disease as the syllabus 200819112. In addition to the hardness index of the CCA, the software also has a different subject of the tester][mt. 3 · 63⁄4 bed test Sampling Average age 39 Normal subject (Normal) age distribution (2〇~73) ±14 (n=36) 〇

Diabetes (DM) age distribution (56~82) (n=28) 〇 Mean age 62 ±8 Cardiac disease patients (CAD) age distribution is 56~82, average 64 5 + 9 (n=7) 〇' 、,·· _ Result a· The healthy ethnic group is proportional to the arterial stiffness and is moderately correlated μ). b. CAD (15.3 ± 6.3 MPa) is higher than the arterial stiffness of the N〇rmal (8.3 ± 3.3 MPa) group (P < 2xl0·6). c. CAD (0.93±0.28 mm) is larger than IMT of N〇rmal (〇.33±0.1 mm) group (P< lxl(T12) 〇d. DM(15±5.9 MPa) than Normal(8.3±3.3 MPa) The arterial stiffness of the ethnic group is high (P<3xl(T7). And e. DM(0.52±0.18mm) is larger than the ΙΜτ of the N0rmal (〇.33±0.lmm) group (Ρ<9χ10·ν f·if considering the traditional The stiffness of the arterial stiffness/?, CAD and DM group are inseparable (P 0.9), using the arterial material hardness index standardized by the arterial wall proposed in this patent, DM (3.1 ± 0.5) material hardening ratio CAD (L9 ± 〇.25) Seriousness (Ρ=0·001) 〇13⁄4 200819112 [Simplified illustration] The first figure is a schematic diagram of the method for detecting the hardness of the non-invasive vascular material of the present invention. CCA Ultrasonic Original Image ® Second Figure B is a CCA slitting area map of the present invention. Second Figure C is a waveform diagram of the CCA slitting area of the present invention as a function of time. The second figure is the CCA vertical of the present invention. The cut-area map is applied to the detection of arterial intima. The fourth panel A is the IMT profile of the present invention. The fourth panel B is the relationship between the longitudinal section area of the artery and the time of the present invention. A is an analytical analysis of the CCA slitting area calculation of the present invention. The fifth drawing B is an analysis of the one-dimensional image Motion-Mode calculation of the present invention. The sixth figure A uses the maximum edge of the echo of the arterial edge echo (Echo) to obtain the coordinates and φ Echo intensity. Figure 6 is a Fast Phase Tracking diagram. Figure 6 is an Echo Tracking Correction diagram. 200819112 [Main component symbol description] 2 Human total carotid artery (CCA) 4 Artery longitudinal imaging device 6 Sphygmomanometer air bag 8 Arterial continuous image composer 10 Sphygmomanometer with output systolic and diastolic pressures 1 2 Image transmission interface 14 Wireless signal transmission input interface (Bluetooth or USB) 1 6 PC platform 18 arterial stiffness analysis software

twenty one

Claims (1)

200819112 X. Patent application scope: 1. A method for detecting the hardness of non-invasive vascular materials, the steps of which include: (4) measuring the blood pressure of the arm blood vessels 1_ and diastolic dust instead of the total carotid artery (CCA); (8) providing-continuous An arterial longitudinal imaging device and a computer analysis platform, and measure the total carotid artery of the human body or other arteries to be measured with appropriate contact force; () display the blood|one image of the image on the screen and adjust the scanning direction to Longitudinal section of the vessel; (d) Confirmation of the correctness of the longitudinal section of the blood section, and determine that the continuous artery longitudinal imaging device does scan the center of the largest diameter of the artery; (e) Transmitting the longitudinal longitudinal image of several heartbeat cycles To a computer platform; Thai (f) converts the true scale of the image pixels from the scale of the image or data; (g) sets the endocardial and adventitial of the initial first image according to the maximum gradient of the hardness change in the vessel wall Edge threshold; (h) Processing of continuous vessel diameter data, calculation of intima-media thickness distribution (intima_mediathickness; mT), and time of arterial diameter Curve; and (i) to estimate the optimal Statistical Theory and Calculation of blood vessel hardness IMT new parameters of 21,200,819,112. 2. The method for measuring the hardness of a non-invasive vascular material as described in the patent application' wherein the appropriate contact force of the aforementioned step (8) is less than that of the diarrhea. 2. The non-invasive vascular material hardness = detection method according to claim 1, wherein the longitudinal section of the artery of the aforementioned step (4) must include an adventitia (AdVentltia) and an intima-media (Intima-Media). Lu ^4·If the hardness of the non-invasive vascular material mentioned in item 1 of the patent scope is included, the method of edge detection of an artery image is included in the method, which uses the fast phase tracking of the edge of the image. Out tons) tips and echo tracking corrections. For example, the double-measurement method for the hardness of non-invasive vascular materials described in item 4 of the patent scope is as follows: the image of the edge of the arterial image is subjected to discrete Fourier transform (DFT) by image gradient or intensity tribute, and several are taken. The phase angle difference of the low frequency, # is corrected by the echo tracking of the fast phase tracking aid, and the actual displacement of the artery wall is extracted. 6. The method for detecting the hardness of a non-invasive vascular material as described in claim 1 wherein the step further comprises utilizing the time shift of the longitudinal section of the arterial image, and using the change in area to estimate the deformation of the artery. 7. A method of detecting the hardness of a non-invasive vascular material as described in the scope of the patent application, wherein the arterial stiffness (anedal) must conform to the Young's coefficient' comprising calculating the arterial stiffness using IMT instead of the overall arterial wall thickness. 200819112 8. The method for detecting the hardness of a non-invasive vascular material according to claim 1, wherein the thickness variation of the ruthenium can be used to calculate the hardness of the material of the layer, including Young's Modulus and shear mode. Quantity (Shear Modulus). 200819112 VII. Designation of representative representatives: (1) The representative representative of the case is: the first picture. (2) A brief description of the symbol of the representative figure: 8. If there is a chemical formula in this case, please disclose the chemical formula that best shows the characteristics of the invention: 2 Total carotid artery (CCA) 4 Arterial longitudinal imaging device 6 Sphygmomanometer air bag 8 Arterial continuous image composer 10 sphygmomanometer with output systolic and diastolic pressures 1 2 image transmission interface 14 wireless signal transmission input interface (blue or USB) 16 PC platform 18 arterial hardness analysis software