2022年单片机的脉搏测量仪的设计开题分析方案6.docx

精品学习资源毕业设计 <论文）材料之二 <2）本科毕业设计 论文>开题报告题目：基于单片机的脉搏测量仪的设计课 题 类 型：设计 错误 .试验讨论论文 学 生 姓 名： 联系扣扣： 2825772782学号：专 业 班 级：学院：电气工程学院指 导 教 师：开 题 时 间2021年 3 月 11 日2021 年 3月 11 日欢迎下载精品学习资源开题报告内容与要求一、毕业设计 <论文）内容及讨论意义 <价值）随着科技进展的不断提高，生命科学和信息科学的结合越来越紧密，显现了各种新奇的脉搏测量仪器，特殊是电子脉搏仪的显现，使脉搏测量变得特别便利；脉诊在我国已具有 2600 多年临床实践，是我国传统中医的精髓，但祖国传统医学采纳“望、闻、问、切”的手段进行病情诊断，受人为的影响因素较大，测量精度不高；科技的创新，脉搏测试不再局限于传统的人工测试法或听诊器测试法，脉搏测量可利用电子仪器测量出精度更就的数据； 人体脉搏信号中包含丰富的生理信息，也逐步引起了临床医生的很大爱好，达到了便利、快捷、精确的测量脉搏的目的；随着电子测量技术 的快速进展，现代电子测量仪器以极快的速度向数字化、自动化的方向进展；制成的 脉搏测量仪器性能良好，结构简洁，有较好的应用和推广价值；脉搏测量仪的设计，必需是通过采集人体脉搏变化引起的一些生物信号，然后把生物信号转化为物理信号，使得这些变化的物理信号能够表达人体的脉搏变化，最终要得出每分钟的脉搏次数，就需要通过相应的硬件电路及芯片来处理物理变化并储备脉搏次数；在硬件设计中一般的物理信号就是电压变化；本系统的组成包括传感器、信号处理、单片机电路、显示电路、键盘输入等部分；联系扣扣： 2825772782二、毕业设计 <论文）讨论现状和进展趋势 <文献综述）随着科学技术的进展，脉搏测量技术也越来越先进，对脉搏的测量精度也越来越高，国内外先后研制了不同类型的脉搏测量仪，脉搏测试不再局限于传统的人工测试法或听诊器测试法，脉搏测量可利用电子仪器测量出精度更就的数据；人体脉搏信号中包含丰富的生理信息，也逐步引起了临床医生的很大爱好，达到了便利、快捷、精确在测量脉搏的目的；随着电子测量技术的快速进展，现代电子测量仪器以极快的速度向数字化、自动化的方向进展；制成的脉搏测量仪器性能良好，结构简洁，有较好的应用和推广价值；而其中关键是对脉搏传感器的讨论；起初用于体育测量的脉搏测试集中在对接触式传感器的讨论，利用此类传感器所研制的指脉、耳脉等测量仪各有其优缺点；指脉测量比较便利、简洁，但由于手指上的汗腺较多，指夹常年使用，污染可能会使测量灵敏度下降：耳脉测量比较洁净，传感器使用环境污染少，简洁保护；但因耳脉较弱，特殊是当季节变化时，所测信号受环境温度影响明显，造成测量结欢迎下载精品学习资源果不精确；过去在医院临床监护和日常中老年保健中显现的日常监护仪器，如便携式 电子血压计，可以完成脉搏的测量 ,但是这种便携式电子血压计利用微型气泵加压橡胶气囊，每次测量都需要一个加压和减压的过程，存在体积巨大、加减压过程会有不适、脉搏检测的精确度低等缺点；脉搏测量仪的进展主要向以下几个趋势进展：<1）自动测量脉搏并且对所得到的脉搏进行自动分析；目前很多脉搏测量仪都具有检测血氧等其他的功能，但是对这些信号的分析和诊断仍需要一些有体会的医生观看，进行分析后才能确认结果，铺张大量的人力，且由人为引入的误差较大；因此，将来脉搏自动检测的内容将更加具体，自动分析诊断功能也更强大；<2） 数字化技术等先进技术的应用；随着数字科学技术的进展，脉搏测量仪集成度将更高，更便于携带；数字信号处理的运用将使干扰更小，测量更为精确；<3）多功能化越来越明显目前的脉搏测量仪，一般都具有测试血氧，心电图等等功能，单纯的脉搏测量仪已经很少见；随着电子技术的进展，脉搏测量仪必定可以实现更多的功能；人体脉搏测试仪是用来测量人体心脏跳动频率的电子仪器，也是心电图的主要组成部分；心脏跳动频率通常用每分钟心脏跳动的次数来表示；采纳数显式脉搏计测量心脏跳动的频率不但精确，而且使用便利，显示结果醒目；近年来国内外致力于开发无创非接触式的传感器，这类传感器的重要特点是测量的探测部分不侵入机体，不造成机体创伤，能够自动排除外表自身系统的误差，测量精度高，通常在体外，特殊是在体表间接测量人体的生理和生化参数；通过查阅资料发觉主要的脉率采集有三种方法：采纳一对红色发光二极管实现、采纳反射式的红外管实现和采纳压电陶瓷芯片实现；方法一：检测的基本原理：随着心脏的搏动，人体组织半透亮度随之转变；当血液送到人体组织时，组织的半透亮度减小；当血液流回心脏，组织的半透亮度增大；这种现象在人体组织较薄的手指尖、耳垂等部位最为明显；因此，本脉率计将红外发光二极管产生的红外线照耀到人体的上述部位，并用装在该部位另一侧或旁边的红外光电管来检测机体组织的透亮程度并把它转换成电信号；由于此信号的频率与人体每分钟的脉搏次数成正比，故只要把它欢迎下载精品学习资源转换成脉冲并进行整形、计数和显示，就能实现实时检测脉搏次数的目的；方法二： 采纳反射式的红外管；现在市场上的脉率计普遍采纳这种传感器来采集信号，由于此红外管接收和发射都在手指的同一侧，所以就不用考虑每个人手指情形不同所造成的麻烦了；但是同样的，对红外的学问明白相对匮乏，得到需要的信号也不太简洁；方法三：采纳压电陶瓷片通过脉搏的跳动采集信号；随着心脏的搏动，人体手腕的脉搏和颈部的搏动较为明显，采纳压电传感器放于上述部位，把压电传感器测得的信号转换成脉冲并进行整形、计数和显示，就能实现实时检测脉搏次数的目的；当脉搏跳动时，压电陶瓷片便会产生相应的信号，虽然这是一种很陈旧的方法，但是却很有用， 测试的时候能够明显的观测到信号的变化；人体心室周期性的收缩和舒张导致主动脉的收缩和舒张，是血流压力以波的形式从主动脉根部开头沿着整个动脉系统传播，这种波成为脉搏波；从脉搏波中提取人体的心理病理信息作为临床诊断和治疗的依据，历来都受到中外医学界的重视；脉搏波所出现出的形状 波形>、强度波幅>、速率波速>和节律周期>等方面的综合信息，在很大程度上反映出人体心血管系统中很多生理病理的血流特点,因此对脉搏波采集和处理具有很高的医学价值和应用前景；但人体的生物信号多属于强噪声背景下的低频的弱信号,脉搏波信号更是低频柔弱的非电生理信号,因此必需经过放大和后级滤波以满意采集的要求；欢迎下载精品学习资源三、毕业设计 <论文）讨论方案及工作方案 <含工作重点与难点及拟采纳的途径）本设计采纳单片机 AT89C51 为掌握核心，实现脉搏测量仪的基本测量功能；系统硬件框图如下图 1 所示：键盘输入脉搏传感器信号放大与整形电路单片机AT89C51显示电路报警电路图 1 脉搏测量仪硬件框图本设计的难点在软件编码与调试这一部分，软件这部分用C 语言编写， C 语言编写比较简洁，而且看起来脉络清楚，明白，易懂；并且调试、修改起来也比较便利；编写时各个模块可以独立编写，各个模块用一个函数表示，需要时只需调用即可，最后再将各个模块联系起来；当然，各个模块程序的编写仍是相当不简洁的，需要多查阅资料与学习；重点在硬件设计，硬件设计主要就是各个模块的设计，其关键在于仪器选型和电路设计，如：显示电路用LED 显示，键盘主要用于设定脉搏波速上下限，不在此范畴，就就报警；这部分也需多查阅资料，多多请教别人，多摸索；欢迎下载精品学习资源起止日期<日/月）周次内容进程备注2.25- 3.31熟识毕业论文的题目，查阅相关的资料工作方案3.4-3.102构思设计模块，撰写开题报告3.11- 3.173理清思路，提出论文设计方案3.18-3.244论证方案3.25-3.3154.1-4.76硬件设计 <各模块设计）4.8-4.1474.15-4.2184.22-4.2894.29-5.510软件编码与调试5.6-5.12115.13-5.19125.20-5.2613撰写论文5.27-6.214完成初稿6.3-6.915修改定稿，送审6.10-6.1616再修改并预备答辩6.17-6.2317答辩6.24-6.3018欢迎下载精品学习资源四、主要参考文献 <不少于 10 篇，期刊类文献不少于7 篇，应有肯定数量的外文文献，至少附一篇引用的外文文献 <3 个页面以上）及其译文）1 程光，赵崇侃指动脉搏波光电传感器的研制J 南京医学院学报， 1991 年第11 卷第 4 期， 3293302 朱国富，廖明涛，王博亮袖珍式脉搏波测量仪J 电子技术应用， 1998，第 1期， 133 韩文波，曹维国，张精慧光电式脉搏波监测系统J 长春光学精密机械学院学报， 1999，第 22 卷第 4 期， 24 欧阳俊，谢定等基于 BL-410 的指端脉搏波采集系统应用讨论 J 有用预防医学， 2004，第 11 卷第 2 期， 245 刘云丽，徐可欣等微功耗光电式脉搏测量仪J 电子测量技术， 2005，第 2期， 256 刘文，杨欣，张铠麟基于 AT89C2051单片机的指脉检测系统的讨论 J 医疗装备， 2005，第 9 期， 2 147 程咏梅，夏雅琴，尚岚人体脉搏波信号检测系统J 北京生物医学工程，2006，第 25 卷第 5 期， 138 李海边 . 单片机技术课程设计与工程实例M.北京：中国电力出版社， 20219 J McLaughlin, M McNeill, B Braun and P D McCormack.Piezoelectricsensordetermination of arterial pulse wave velocity M. UK： INSTITUTE OF PHYSICS PUBLISHING ， 2003, 6-4.10 J.C.Candy and G.C.TemesOversampling Methods for Data ConversionM IEEE Pacific Rim conference on Communications， Computers and Signal Processing， May 1991， 9-1011 John DRyder Electronic Fundamentals and ApplicationsM1983，1-24欢迎下载精品学习资源外文文献：Piezoelectric sensor determination of arterial pulse wavevelocityArterial pulsewave velocity APWV> is ameasure of the elasticity or stiffness>of peripheral arterial blood vessels. The pulse referred to here will be thepressure pulse as opposed to the flow pulse measured by ultrasound Doppler.The pressure pulse velocity varies over the range from about 12 m s-1 to15 m s-1 in stiff pe ripheral arteries, whereas in normal arteries it has a velocityin the range of 7 to 9 m s-1.The aimof this projectwas the development of a fast and easy to use systemfor the determinationofperipheralarterialpulse wavevelocity.Theprincipleofthe PWV measurement is based on simultaneous measurement of two pulsewaves at two different positions, such as the radial artery at the wrist andthe brachial artery just above the elbow. By determining the pulse transit timebetween these points and the distance measured between the two locations,pulse wave velocity may then be calculated. The pressure pulse detection isdone by using two piezoelectric sensors which generate a measurable voltageat the output contacts if they are mechanically deformed. The deformationproduced voltage is first amplified and filtered and then digitalized with a dataacquisition card. The analysis of the data obtainedfrom the sensors includesa filtering process, the calculation of the PWV with three different methodsfoot-to-foot,cross-correlationandpeak-to-peakandthedeterminationof thearterial pulse rate.Thesensor technique used inthisworkinvolvesthepiezoelectriceffectin polyvinylidene fluoride PVDF>, which produces an output voltage in response to mechanical pressure on the material.Three methods of APWV determination are used: foot-to-foot APWV ； peak-to-peakAPWVand cross-correlationAPWV. The FFAPWV and CCAPWVmethods are less sensitive to pressure wave reflections at bifurcations, etc inthe arterial tree, than the PPAPWV method. Mean values and standard deviations were computed for all three methods and compared. Foo-tto-foot APWV FFAPWV>. This is based on the velocity of the foot ,edge, of the pressure pulse wave. The arrival times of the foot of the pulse wave attwopositions along the artery are recorded. Ift is the difference in arrival times ands thedistance between the two recording positions proximal and distal>, the FFAPWV is simplyFFAPWV = s/t.欢迎下载精品学习资源 Pea-tko-peak APWV PPAPWV>. This icsompletely analogous to the FFAPWVexcept that the points of observation are the two proximal and distal> peaks of the pulse waveandPPAPWV = s/t.Apparent pulse wave velocity AAPWV>. The pressure wave may be represented as a Fourier series,Pt> = P0 +Pn sinn t + n>WhereP0 is the mean fluid pressure, n is the harmonic number, Pn is the amplitude of the nthharmonic andn is the phase angle of the nth harmonic.The spatial rate of change of the phase for one harmonic based on two simultaneouspressure measurements separated by a distance _s along an artery, is related to the apparentarterial pulse wave velocity AAPWV> by the following equation,AAPWVn = s>nf >360o>/x1- x2>WhereAAPWVn is the apparent pulse wave velocity for the nth harmonic, f is the heart rate,x1 is the phase angle for the proximal harmonic n andx2 is the phase angle for the distalharmonic n.Cross-correlation PWV. If the arterial pulse at the proximal measurement position isrepresented by the pressure time series Px1, t> and that at the distal position by Px2, t> andthe cross-correlation coefficient isx1,x2 >, then will have a maximum value at some timelag.The correlation function can be expressed asx1,x2 > = 1/T >Px1, t>Px2, t> dt.The value of at whichmaximumcorrelation occurs represents the transit time _t> of thepressure wave from position x1 to position x2 along the arterial segment. From the separationdistance and transit time data the correlation arterial pulse wave velocity isCCAPWV = x2 - x1>/t.In this work normal, young test subjects were used, and it has the primary objectives of optimizing the measurement procedures and establishing the statistical spread and mean values of the observed PWVs for a specific peripheral arterial segment. Based on this, it is planned to use the system in clinical trials involving patients with peripheral arterial disease due to diabetes, hypertension, etc>, pre-, during and post treatment pharmaceutical or surgical>.欢迎下载精品学习资源Analogue and digital circuitryAnalogue charge amplifier. Piezoelectricmaterials convert mechanical stress or strain into proportionate electrical energy, by producing a charge when subjected to mechanicalstress. The charge is converted to a voltage by an operational amplifier connected as a current integrator, called a charge amplifier. The signal output of the amplifier is approximately -30 mV. It is augmented by signal amplification.Analogue signal amplification . This is done by use of an inverting amplifier. Because a dc signal appears at the output of the charge amplifier, dc offset removal is essential and is implemented in the inverting summingThe next phase of the analogue circuitry is a low pass filter to remove the 50 Hz noiseinterference.Digital controlled data acquisition and analysis. A data acquisition board DAQ> is required when the transducer signals need interfacing with a PC. The board contains 12 bit plus sign and a successive approximation and self-calibrating analogue-to-digital ADC> converter. The ADC incurs a systematic error known as the quantization error. It is due to limited resolution and with the analogue input limit set at -5 to +5 V, the quantization error of the A/D converter used here was calculated to be 0.122 m. VThe data acquisition and analysis was done using Lab View a powerful instrumentation and analysis programming language for PCs.Digital data acquisition program. The data acquisition circuit performs all the necessary operations for the data acquisition with Lab View. The functions of the circuit initialize thedata acquisition and read the data from the acquisition card. These data are stored for later usein the data analysis part of the program.Lab View programs are called virtual instruments VIs> because of their appearance and operations are analogous to measuring instruments. A VI that is called within another VI is called a sub-VI and is analogous to a subroutine in text-based languages.The data acquisition, analysis and presentation are comprised of three main procedures:1> Data acquisition card to interface the hardware to the PC.2> Data acquisition program to acquire and store data in a spreadsheet file.3> Data analysis to carry out digital signal processing, calculate PWV and present results.PWV Calculation1. PWV calculation using peak detection. To calculate PWV using peaks, the location of the peaks must first be determined, so that the transit time of the wave between the peaks can be determined. It was found that the best method of peak detection is the derivative of the curve method. If the first derivative of a curve is zero, then an extreme value can exist eithera peak or a turning point. It is necessary to take the second derivative at this pointif this isalso zero, then an extreme value exists. The second VI used to determine the PWV is PWVcalc, using the time separation between the located peaks.2. PWV with pressure wave foot detection. The VI named PWV Foot determines theleading edge foot> of the pressure wave at the upstream and downstream locations. The VI named PWVcalc is again used to compute the PWV from the time separation between the two leading edges -tof-ofoot t APWV or FFAPWV>.3. PWV with cross-correlation. The PWV determination with cross-correlation is done欢迎下载精品学习资源with the VI named CalcPWV. The VI is in two parts: a part for the initialization function and a part for the calculation of the CCAPWV.In all cases PWV values are assembled in an array and the mean value, standarddeviation and variance are calculated.Sensor positioningSensor placement is critical to obtaining consistent measurements. A screw mechanism was first used to apply the sensors to the skin. But readings were very variable and so this technique was replaced by that in which the sensors are fixed to the skin by elastic strips. This led to better results.Arm position is another critical feature of measurement. Two positions, normal and dependent, were analyzed in detail, using one test subject. In the normal position, the subject sits with the arm resting on a table. All test subject measurements were made in this position. In the dependent position, the subject sits with the arm hanging straight down.The PWV values were smaller in this position and the variability was much greater, so this technique was discarded.A correction module, Delete Incorrect, was used to delete PWV values resulting froaberrant signals, caused commonly by arm movement during the measurement. These unrealistic values were deleted before the PWV values were passed to the analysis VI.中文翻译压电传感器测定动脉脉搏波速度动脉脉搏波速度 APWV>是一个测量的弹性 或刚度 >的外周动脉血管；这里指的脉 冲将压力脉冲 , 而不是流脉冲多普勒超声测量；压力脉冲速度变化范畴从12ms- 1 到15ms- 1, 而在正常动脉有速度范畴 , 在 7 到 9 ms- 1；这个工程的目标是开发一种快速和易于使用的系统测定外周动脉脉搏波速度；测量仪的原理是基于同时测量两个脉冲波在两个不同的位置, 比如桡动脉在手腕和上臂肱动脉略高于肘部；通过测定脉冲过境时间这些点之间和距离测量这两个地点, 脉搏波速度可能会被运算；压力脉冲检测是通过使用两个压电传感器产生一个可测量的电压输出联系人假如他们是机械变形；变形产生电压是第一放大和过滤, 然后用数据采集卡数字化；分析中获得的数据传感器包括一个过滤过程中, 运算有三种不同的方法 foot- to-foot APWV ；peak-to-peak APWV 和 cross-correlation APWV；传感器技术用于这项工作涉及到压电效应在聚偏二氟乙烯PVDF>,它产生一个输出电压响应机械压力对材料；三种测定动脉脉搏波速度的方法是 : foot-to-foot APWV ；peak-to-peak APWV and cross-correlation APWV；FFAPWV和CCAPWV 方法不敏锐 , 压力波反射在分支等在动脉树, 比如PPAPW方V法；平均值和标准偏差是这三种方法分别要运算并比较的； Foo-tto-foot APWVFFAPWV；> 这是基于压力脉冲波速度的 “脚”或,前缘；脚的到达时间的脉冲波在两个位置沿动脉被记录； t是到达时间之差和 s是两个记录位置 近端和远端 >之间的距离 ,FFAPWV 是欢迎下载精品学习资源FFAPWV = s / ；t欢迎下载精品学习资源 Pea-tko-peak APWVPPAPWV；>冲波的两个 近端和远端 >的山峰这是完全类似于FFAPWV，只是点的观测是