技术领域Technical Field
本发明涉及生物组织电磁检测领域，尤其涉及生物组织高频（>1GHz）电磁非侵入性创口在体监测探头及其测量方法。该发明适用于生物体外创伤口状况的实时、在体监测。易共形、可小型化，有较高的便携性能与测量精度，具有很好的应用前景。The present invention relates to the field of electromagnetic detection of biological tissues, and in particular to a high-frequency (>1GHz) electromagnetic non-invasive in-vivo monitoring probe for biological tissue wounds and a measurement method thereof. The invention is suitable for real-time in-vivo monitoring of the condition of in-vivo wounds. It is easy to conform, can be miniaturized, has high portability and measurement accuracy, and has good application prospects.
背景技术Background technique
创口愈合对伤者而言是非常重要且漫长的过程。对创口进行监测，不仅可以实时了解创口状况，进而对其进行有效处理，还可以为创口评估和治疗计划提供实时有效的信息。此外，也给临床研究提供了可靠的信息资源。因此，创口监测具有十分重要的应用价值与研究意义。Wound healing is a very important and long process for the injured. Monitoring the wound can not only understand the wound condition in real time and effectively treat it, but also provide real-time and effective information for wound assessment and treatment plan. In addition, it also provides a reliable information resource for clinical research. Therefore, wound monitoring has very important application value and research significance.
现代医疗健康领域正逐渐向数字化、网络化、家庭化不断转变。这意味着医疗监测技术应更加高效，准确，方便且无创，以适应现实中各领域需求，例如工程，军事等。现有的创口监测技术主要基于临床人员的经验，通过诸如创口面积和深度的物理学测量或诸如细胞迁移实验等生理测量进行评估。但这些方法便捷性与实时性不高。以光学相干断层扫描（OCT）为代表的物理图像技术具有良好的实时性能，并满足高精度和非侵入性要求。然而，OCT检测容易受到诸如绷带，药物，血流等外部因素的干扰，并且由于光学仪器的敏感性，其监测成本相对较高。The modern medical and health field is gradually shifting towards digitalization, networking, and home-based. This means that medical monitoring technology should be more efficient, accurate, convenient, and non-invasive to meet the needs of various fields in reality, such as engineering, military, etc. Existing wound monitoring technology is mainly based on the experience of clinical personnel and is evaluated through physical measurements such as wound area and depth or physiological measurements such as cell migration experiments. However, these methods are not very convenient and real-time. Physical imaging technology represented by optical coherence tomography (OCT) has good real-time performance and meets high precision and non-invasive requirements. However, OCT detection is easily interfered by external factors such as bandages, drugs, blood flow, etc., and its monitoring cost is relatively high due to the sensitivity of optical instruments.
发明内容Summary of the invention
本发明的目的在于，提供一种可实时监测生物体外创口状况的非侵入性测量探头及相应的测量方法。该探头具备良好的共形特性，可贴附于绷带等护创材料之间，防止与创口直接接触，实现非侵入性，且探头易于小型化，便携性能和组阵特性较高；测量方法基于传输线理论，可实时获取多个特征参数，提高测量结果的精确度。探头组阵后还可以基于测量参数实现成像效果，成像分辨率较高。The purpose of the present invention is to provide a non-invasive measurement probe and a corresponding measurement method that can monitor the wound condition outside a living body in real time. The probe has good conformal properties and can be attached between wound protection materials such as bandages to prevent direct contact with the wound, thereby achieving non-invasiveness. The probe is easy to miniaturize, and has high portability and array characteristics. The measurement method is based on transmission line theory, and multiple characteristic parameters can be obtained in real time to improve the accuracy of the measurement results. After the probe is arrayed, an imaging effect can be achieved based on the measurement parameters, and the imaging resolution is high.
为了实现上述任务，本发明采取如下的技术解决方案予以实现：In order to achieve the above tasks, the present invention adopts the following technical solutions:
一种非侵入性体外创伤监测探头，包括中心金属导带、外边沿金属极板、介质基板，中心金属导带和外边沿金属极板同侧位于介质基板之上，且中心金属导带与外边沿金属极板之间留有间隙；A non-invasive in vitro trauma monitoring probe comprises a central metal conductive strip, an outer edge metal plate, and a dielectric substrate, wherein the central metal conductive strip and the outer edge metal plate are located on the dielectric substrate on the same side, and a gap is left between the central metal conductive strip and the outer edge metal plate;
分别贯穿金属导带、外边沿金属极板和介质基板两端开设过孔，形成同轴馈电激励端口。Vias are respectively provided through the metal conducting strip, the outer edge metal plate and both ends of the dielectric substrate to form a coaxial feeding excitation port.
进一步地，贯穿金属导带、外边沿金属极板和介质基板两端的过孔对称设置。Furthermore, the via holes penetrating the metal conducting strip, the outer edge metal plate and the two ends of the dielectric substrate are symmetrically arranged.
所述的金属导带、外边沿金属极板的两端均为弧形，且金属导带的弧顶与外边沿金属极板内侧两端弧顶共圆心设置。Both ends of the metal conductive strip and the outer edge metal plate are arc-shaped, and the arc top of the metal conductive strip and the arc tops of the inner two ends of the outer edge metal plate are arranged co-centrically.
所述的介质基板的材料为柔性电路基板FPC，金属导带与外边沿金属极板的材料为金或者表面镀金的铜。The material of the dielectric substrate is a flexible circuit substrate FPC, and the material of the metal conductive strip and the outer edge metal plate is gold or copper with gold-plated surface.
本发明还公开了一种监测探头的体外创伤监测方法，该方法包括如下步骤：The present invention also discloses an in vitro trauma monitoring method using a monitoring probe, the method comprising the following steps:
1）选择监测探头A和监测探头B；1) Select monitoring probe A and monitoring probe B;
2）将监测探头置于包裹创口的创护材料中间，其中，探头与创口之间的护创材料厚度不超过10mm；监测探头的金属导带（101）面朝向创口表面，探头的介质基板（103）面继续包覆创护材料。该探头作为创口监测探头A；将另一个探头置入包裹监测探头A的创护材料，然后将整体置于空气中作为标校监测探头B；2) Place the monitoring probe in the middle of the wound protection material covering the wound, wherein the thickness of the wound protection material between the probe and the wound does not exceed 10 mm; the metal conductive tape (101) of the monitoring probe faces the wound surface, and the dielectric substrate (103) of the probe continues to cover the wound protection material. This probe serves as wound monitoring probe A; place another probe in the wound protection material covering monitoring probe A, and then place the whole in the air as calibration monitoring probe B;
3）分别将创口监测探头A、标校监测探头B的馈电端通过同轴电缆连接到矢量网络分析仪上，工作频率>1GHz，测量得到标校监测探头B、创口监测探头A的二端口网络散射矩阵S0和S1：3) Connect the feed end of wound monitoring probe A and calibration monitoring probe B to a vector network analyzer through coaxial cables, with an operating frequency of >1GHz, and measure the two-port network scattering matricesS0 andS1 of calibration monitoring probe B and wound monitoring probe A:
（1） (1)
公式(1)中，Sij为探头的二端口网络散射矩阵S参数，表示其他端口匹配时，端口j到端口i的传输系数；In formula (1),Sij is the two-port network scattering matrix S parameter of the probe, which represents the transmission coefficient from portj to porti when the other ports are matched;
4）根据参数S0和S1进一步计算标校监测探头B、 创口监测探头A的二端口网络阻抗矩阵Z0和Z1，具体计算公式如下：4) The two-port network impedance matricesZ0 andZ1 of the calibration monitoring probe B and wound monitoring probe A are further calculated based on the parametersS0 andS1. The specific calculation formula is as follows:
（2） (2)
公式(2)中，Ziij为探头的二端口网络阻抗矩阵Zi参数，表示端口j到端口i的转移阻抗，Zc为探头馈电端口的特性导纳，I为单位矩阵；In formula (2),Ziijis the two-port network impedance matrixZiparameter of the probe, which represents the transfer impedance from portj toporti ,Zc is the characteristic admittance of the probe feeding port,andI is the unit matrix;
5）将创口监测探头A的二端口网络阻抗矩阵Z1减去标校监测探头B的二端口网络阻抗矩阵Z0，最终得到标校后的创口监测探头A的二端口网络阻抗矩阵Z=Z1-Z0参数；5) Subtract the two-port network impedance matrixZ0 of the calibration monitoring probe B from the two-port network impedance matrixZ1 of the wound monitoring probe A, and finally obtain the two-port network impedance matrixZ =Z1 -Z0 parameters of the calibrated wound monitoring probe A;
6）针对创口监测探头A的二端口网络建立“T”型等效电路模型，并对标校后的创口监测探头A的二端口网络阻抗矩阵Z=Z1-Z0参数进行数据处理，“T”型等效电路由复阻抗Z1、Z2、Z3组成，且满足如下关系：6) A "T" type equivalent circuit model is established for the two-port network of the wound monitoring probe A, and the parameters of the two-port network impedance matrixZ =Z1 -Z0 of the wound monitoring probe A after calibration are processed. The "T" type equivalent circuit consists of complex impedancesZ1 ,Z2 , andZ3 , and satisfies the following relationship:
（3） (3)
7）针对复阻抗Z1、Z2、Z3的实部和虚部，在最大谐振频率点f0附近构建频率分布模型，模型中复阻抗Z1、Z2、Z3的实部和虚部与工作频率f之间满足如下关系：7) For the real and imaginary parts of the complex impedancesZ1 ,Z2 , andZ3 , a frequency distribution model is constructed near the maximum resonant frequency pointf0 . In the model, the real and imaginary parts of the complex impedancesZ1 ,Z2 , andZ3 satisfy the following relationship with the operating frequencyf :
（4） (4)
其中，q1、q2均为常数，pi（i=1~24）为被测生物体创口处的介电特性参数；Among them,q1 andq2 are constants, andpi (i = 1~24) is the dielectric property parameter of the wound of the measured biological body;
8）对步骤7）复阻抗Z1、Z2、Z3的模型参数pi（i=1~24）进行主成分分析，从中提取参数m1、m2，参数m1、m2与pi之间满足如下关系：8) Perform principal component analysis on the model parameterspi (i = 1-24) of the complex impedancesZ1 ,Z2 , andZ3 in step 7) to extract parametersm1 and m2 . The following relationship is satisfied between the parametersm1 ,m2 andpi :
（5） (5)
其中，矩阵C（24×2矩阵）为参数pi（i=1~24）的特征矩阵；Among them, the matrix C (24×2 matrix) is the characteristic matrix of parameterpi (i =1~24);
9）将步骤5）得到的将标校后的创口监测探头A的二端口网络阻抗矩阵Z=Z1-Z0参数和步骤8）得到的被测生物体创口处的介电特性参数，构建创口状态管理数据库；对创口状态进行管理分类，并提取分类中心：Mi为创口状态的参数矩阵中心，i为创口状态类别；9) The two-port network impedance matrixZ =Z1 -Z0 parameters of the calibrated wound monitoring probe A obtained in step 5) and the dielectric characteristic parameters of the wound of the measured biological body obtained in step 8) are used to construct a wound state management database; the wound state is managed and classified, and the classification center is extracted:Mi is the parameter matrix center of the wound state,and i is the wound state category;
10）基于创口状态管理数据库中创口状态类别，对探头测量获取的主要参数M=[m1,m2]进行聚类分析并判别，当Pi=1时，i所对应的创口状态类别即为当前创口状态。10) Based on the wound status categories in the wound status management database, cluster analysis and discriminationare performed on the main parameters M=[m1 ,m2 ] obtained by the probe measurement. WhenPi = 1, the wound status category corresponding toi is the current wound status.
优选地，步骤4）中Zc=50 Ω。Preferably, in step 4),Zc =50 Ω.
本发明的非侵入性外创伤在体监测探头和现有技术相比，具有以下的优势：Compared with the prior art, the non-invasive trauma monitoring probe of the present invention has the following advantages:
1. 测量无需直接接触组织，对生物组织既没有破坏性，也不会造成与生物组织之间的交叉污染。1. The measurement does not require direct contact with the tissue, is non-destructive to the biological tissue, and will not cause cross contamination with the biological tissue.
2. 探头选用柔性基底材质，共形能力高，测量受组织形状的影响较低。2. The probe is made of flexible substrate material with high conformal ability, and the measurement is less affected by tissue shape.
3. 探头整体轻薄，尺寸较小（与创可贴尺寸规格相当），便携性高，且易于多个探头进行组阵实现成像监测。3. The probe is thin and light overall, with a small size (comparable to the size of a Band-Aid), high portability, and easy to group multiple probes for imaging monitoring.
4. 探头工作频段较高（>1GHz），易于获取较高的信息分辨率。4. The probe has a high operating frequency band (>1GHz), making it easy to obtain higher information resolution.
附图说明BRIEF DESCRIPTION OF THE DRAWINGS
图1是本发明探头结构的正视图、背视图与侧视图。其中，图（1a）是探头结构的正视图，图（1b）是探头结构的背视图，图（1c）是图（1a）的左侧视图。Fig. 1 is a front view, a back view and a side view of the probe structure of the present invention, wherein Fig. (1a) is a front view of the probe structure, Fig. (1b) is a back view of the probe structure, and Fig. (1c) is a left side view of Fig. (1a).
图2是本发明探头的中心金属导带的正视图与侧视图。其中，图（2a）是金属导带的正视图，图（2b）是图（2a）的前侧视图，图（2c）是图（2a）的左侧视图。Figure 2 is a front view and a side view of the central metal conductive strip of the probe of the present invention, wherein Figure (2a) is a front view of the metal conductive strip, Figure (2b) is a front side view of Figure (2a), and Figure (2c) is a left side view of Figure (2a).
图3是本发明探头的金属极板的正视图与侧视图。其中图（3a）是极板的正视图，图（3b）是图（3a）的左侧视图。Fig. 3 is a front view and a side view of the metal electrode plate of the probe of the present invention, wherein Fig. (3a) is a front view of the electrode plate, and Fig. (3b) is a left side view of Fig. (3a).
图4是本发明探头的介质基板的正视图与侧视图。其中图（4a）是介质基板的正视图，图（4b）是图（4a）的左侧视图。Fig. 4 is a front view and a side view of the dielectric substrate of the probe of the present invention, wherein Fig. (4a) is a front view of the dielectric substrate, and Fig. (4b) is a left side view of Fig. (4a).
图5是本发明探头的过孔位置示意图。FIG. 5 is a schematic diagram of the via hole position of the probe of the present invention.
图6是本发明实施例中的仿真结构模型示意图。FIG. 6 is a schematic diagram of a simulation structure model in an embodiment of the present invention.
图7是本发明测量方法中针对探头的二端口网络建立的“T”型等效电路阻抗模型。FIG. 7 is a “T” type equivalent circuit impedance model established for the two-port network of the probe in the measurement method of the present invention.
图8是本发明实施例中的各生物组织介电特性参数。其中图（8a）是各组织的介电系数，图（8b）是各组织的电导率。FIG8 shows the dielectric property parameters of various biological tissues in an embodiment of the present invention, wherein FIG8a shows the dielectric constant of each tissue, and FIG8b shows the conductivity of each tissue.
图9是本发明实施例中探头两端不同结构设计下探头监测正常组织和异常组织阻抗结果对比图。其中图(9a)是探头两端开路设计下阻抗实部对比图，图(9b)是探头两端开路设计下阻抗虚部对比图，图(9c)是探头两端矩形封闭设计下阻抗实部对比图，图(9d)是探头两端矩形封闭设计下阻抗虚部对比图，图(9e)是本发明结构设计下阻抗实部对比图，图(9f)是本发明结构设计下阻抗虚部对比图。FIG9 is a comparison diagram of the impedance results of normal tissue and abnormal tissue monitored by the probe under different structural designs at both ends of the probe in an embodiment of the present invention. FIG9a is a comparison diagram of the real part of the impedance under the open circuit design at both ends of the probe, FIG9b is a comparison diagram of the imaginary part of the impedance under the open circuit design at both ends of the probe, FIG9c is a comparison diagram of the real part of the impedance under the rectangular closed design at both ends of the probe, FIG9d is a comparison diagram of the imaginary part of the impedance under the rectangular closed design at both ends of the probe, FIG9e is a comparison diagram of the real part of the impedance under the structural design of the present invention, and FIG9f is a comparison diagram of the imaginary part of the impedance under the structural design of the present invention.
图中的标号分别表示：101、中心金属导带，102、金属极板，103、介质基板，104、过孔，105、馈电同轴，106、仿真绷带，107、仿真皮肤组织，108、仿真脂肪组织，109、仿真肌肉组织，110、仿真创口。The numbers in the figure represent respectively: 101, central metal conduction band, 102, metal electrode plate, 103, dielectric substrate, 104, via hole, 105, feeding coaxial, 106, simulated bandage, 107, simulated skin tissue, 108, simulated fat tissue, 109, simulated muscle tissue, 110, simulated wound.
以下结合附图以及发明人提供的原理和实施例，对本发明做进一步说明。The present invention is further described below in conjunction with the accompanying drawings and principles and embodiments provided by the inventor.
具体实施方式Detailed ways
本发明探头的工作原理在于：由于探头附近的生物体创口部位组织与正常部位组织介电系数与电导率的差异性，导致电磁场在探头馈电端口之间传播过程中的相位变化和幅度损耗有所不同。这种差异性会导致仪器测量电磁场在探头馈电端口之间传播的传输参数的不同。通过建立模型提取主要分析参数，就可以根据这些参数对比数据库信息，进而判别生物体创口状况信息。The working principle of the probe of the present invention is that due to the difference in dielectric constant and conductivity between the tissue of the wound part of the organism near the probe and the tissue of the normal part, the phase change and amplitude loss of the electromagnetic field during the propagation between the probe feeding ports are different. This difference will cause the instrument to measure the difference in the transmission parameters of the electromagnetic field propagating between the probe feeding ports. By establishing a model to extract the main analysis parameters, the database information can be compared based on these parameters to further determine the information on the wound condition of the organism.
基于以上原理，本实施例给出一种非侵入性外创伤在体监测探头及测量方法，其结构组成与工作方式如下：Based on the above principles, this embodiment provides a non-invasive external trauma in-body monitoring probe and measurement method, the structure and working mode of which are as follows:
参考图1，本实施例给出一种非侵入性外创伤在体监测探头。该探头主要由四部分组成：第一部分是中心金属导带101，第二部分是外边沿金属极板102，第三部分是介质基板103，第四部分是过孔104。Referring to FIG1 , this embodiment provides a non-invasive external trauma monitoring probe, which is mainly composed of four parts: the first part is a central metal conductive strip 101 , the second part is an outer edge metal plate 102 , the third part is a dielectric substrate 103 , and the fourth part is a via 104 .
其中，中心金属导带101和外边沿金属极板102位于介质基板103之上，且与外边沿金属极板102之间留有间隙；The central metal conductive strip 101 and the outer edge metal plate 102 are located on the dielectric substrate 103, and a gap is left between the central metal conductive strip 101 and the outer edge metal plate 102;
分别贯穿金属导带101、外边沿金属极板102和介质基板103两端开设过孔104，形成同轴馈电激励端口。Via holes 104 are respectively provided through the metal conductive strip 101 , the outer edge metal plate 102 and both ends of the dielectric substrate 103 to form a coaxial feeding excitation port.
贯穿金属导带101、外边沿金属极板102和介质基板103两端的过孔104对称设置。The via holes 104 penetrating the metal conductive strip 101 , the outer edge metal plate 102 and both ends of the dielectric substrate 103 are symmetrically arranged.
金属导带101、外边沿金属极板102的两端均为弧形，且金属导带101的弧顶与外边沿金属极板102内侧两端弧顶共圆心设置。常规CPW传输线结构只有中心导带与两边极板并没有考虑两端处的设计。但两端的结构设计必然会对产生能量反射，进而影响到监测结果的灵敏度。Both ends of the metal conductive strip 101 and the outer edge metal plate 102 are arc-shaped, and the arc top of the metal conductive strip 101 is co-centered with the arc tops of the inner two ends of the outer edge metal plate 102. The conventional CPW transmission line structure only has a central conductive strip and two side plates, and does not consider the design at the two ends. However, the structural design at the two ends will inevitably produce energy reflection, thereby affecting the sensitivity of the monitoring results.
参见图9，为了尽可能减少两端反射对监测结果带来的影响。通过几种不同类型的结构（两端开路、两端矩形封闭、本发明结构）对比研究，发现当两端以共圆心圆弧形式封闭时，可以最大限度的减少能量反射，进而提高探头监测的灵敏度，进而最终确定了探头两端的结构形式。See Figure 9. In order to minimize the impact of reflection at both ends on the monitoring results, through comparative studies of several different types of structures (open circuit at both ends, rectangular closed at both ends, and the structure of the present invention), it is found that when the two ends are closed in the form of co-centered arcs, energy reflection can be minimized, thereby improving the sensitivity of the probe monitoring, and finally determining the structural form of the two ends of the probe.
介质基板103的材料为柔性电路基板FPC（聚酰亚胺占比90%），金属导带101与极板（102）材料为铜，表面有镀层，镀层采用金材料进行涂镀处理。探头整体尺寸规格为：83.45*23.45*0.135（长*宽*厚，单位mm）。The material of the dielectric substrate 103 is a flexible circuit substrate FPC (90% polyimide), the metal conductive strip 101 and the electrode plate (102) are made of copper, and the surface is plated with a gold material. The overall size of the probe is: 83.45*23.45*0.135 (length*width*thickness, unit: mm).
参考图2，中心金属导带101两端弧顶圆心间距l1=60mm，金属导带101上过孔104的中心间距l2=55.92mm，金属导带101宽度d1=3.15mm，金属导带101厚度h1=0.035mm。2 , the distance between the arc tops of the two ends of the central metal conductive strip 101is l1 =60 mm, the center distance between the via holes 104 on the metal conductive strip 101 isl2 =55.92 mm, the width of the metal conductive strip 101 isd1 =3.15 mm, and the thickness of the metal conductive strip 101is h1 =0.035 mm.
参考图3，金属极板102内部间隙宽度d3=3.45mm，金属极板102宽度d2=23.45mm，金属极板102厚度为h1=0.035mm。3 , the internal gap width of the metal electrode plate 102is d3 =3.45 mm, the width of the metal electrode plate 102is d2 =23.45 mm, and the thickness of the metal electrode plate 102 ish1 =0.035 mm.
参考图4，介质基板103厚度h2=0.1mm。4 , the dielectric substrate 103 has a thicknessh2 =0.1 mm.
参考图5，过孔104孔径d5=1.3mm，过孔104中心间距d4=5.08mm。本实施例监测探头，在过孔104处与标准SMA馈电接头（SMA-KHD100）进行焊接，以此作为探头的馈电端口，并通过转接电缆与矢量网络分析仪连接。5 , the aperture of via hole 104is d5 =1.3 mm, and the center distance of via hole 104is d4 =5.08 mm. The monitoring probe of this embodiment is welded with a standard SMA feeding connector (SMA-KHD100) at via hole 104 to serve as the feeding port of the probe, and is connected to the vector network analyzer through a switching cable.
参考图6，利用本实施例给出的监测探头对人体外创伤（发生流血）的创口状态进行监测，其测量方法按下列步骤进行：6 , the monitoring probe provided in this embodiment is used to monitor the wound state of external trauma (bleeding) of the human body, and the measurement method is performed according to the following steps:
1）选择监测探头A和监测探头B；1) Select monitoring probe A and monitoring probe B;
2）根据实际情况将监测探头A金属导带101面朝向创口部位110并贴附于生物体创口部位110与护创材料绷带106之间，其中金属导带101与创口之间包覆的创护材料厚度为2mm；探头A的介质基板103后面可继续包覆护创材料；监测探头B置入包裹监测探头A的创护材料，然后将整体置于空气中作为标校监测探头B；这个条件非常重要，超过10mm监测灵敏度不可靠了。2) According to the actual situation, the metal conductive tape 101 of the monitoring probe A is facing the wound part 110 and attached between the wound part 110 of the biological body and the wound protection material bandage 106, wherein the thickness of the wound protection material wrapped between the metal conductive tape 101 and the wound is 2 mm; the back of the dielectric substrate 103 of the probe A can continue to be coated with the wound protection material; the monitoring probe B is placed in the wound protection material wrapped around the monitoring probe A, and then the whole is placed in the air as a calibration monitoring probe B; this condition is very important, and the monitoring sensitivity will be unreliable if it exceeds 10 mm.
3）将探头的馈电端通过同轴电缆连接到矢量网络分析仪上，工作频率为1 GHz ~6GHz，分别测量得到探头B与A的二端口网络散射矩阵S0和S1：3) Connect the feed end of the probe to a vector network analyzer via a coaxial cable, with an operating frequency of 1 GHz to 6 GHz, and measure the two-port network scattering matricesS0 andS1 of probes B and A respectively:
4）根据参数S0和S1进一步计算探头B与A的二端口网络阻抗矩阵Z0和Z1。其具体计算方法如下：4) Further calculate the two-port network impedance matricesZ0 andZ1 of probes B and A based on parametersS0 andS1. The specific calculation method is as follows:
公式(13)中，Zc为本实施例给出探头的馈电端口特性导纳，Zc=50 Ω。I为单位矩阵。In formula (13),Zc is the characteristic admittance of the feeding port of the probe given in this embodiment,Zc =50 Ω.I is the unit matrix.
5）将创口监测探头A的二端口网络阻抗矩阵Z1减去标校探头B的二端口网络阻抗矩阵Z0，最终得到标校后的创口监测探头A的二端口网络阻抗矩阵Z=Z1-Z0参数。5) Subtract the two-port network impedance matrixZ0 of the calibration probe B from the two-port network impedance matrixZ1 of the wound monitoring probe A, and finally obtain the two-port network impedance matrixZ =Z1 -Z0 parameters of the calibrated wound monitoring probe A.
6）参考图7，针对创口监测探头A的二端口网络建立“T”型等效电路模型，该电路主要由复阻抗Z1、Z2、Z3组成，其与探头A标校后得到的二端口网络阻抗矩阵Z参数之间满足如下关系：6) Referring to FIG7 , a “T” type equivalent circuit model is established for the two-port network of wound monitoring probe A. The circuit is mainly composed of complex impedancesZ1 ,Z2 , andZ3 , which satisfy the following relationship with the two-port network impedance matrix Z parameters obtained after calibration of probe A:
参考图6，由于本实施例给出的创口具有结构对称性，因此有：Z1=Z2=Z11+Z21，Z3=Z21。Referring to FIG6 , since the wound provided in this embodiment has structural symmetry,Z1 =Z2 =Z11 +Z21 ,Z3 =Z21 .
7）针对复阻抗Z1、Z3的实部和虚部，在最大谐振频率点f0=2.6 GHz附近构建频率分布模型（频带为2~3 GHz），模型中复阻抗Z1、Z3的实部和虚部与工作频率f之间满足如下关系：7) For the real and imaginary parts of the complex impedancesZ1 andZ3 , a frequency distribution model (frequency band is 2~3 GHz) is constructed near the maximum resonant frequency pointf0 =2.6 GHz. In the model, the real and imaginary parts of the complex impedancesZ1 andZ3 and the operating frequencyf satisfy the following relationship:
（） （）
公式(15)中，分母参数q1、q2均为常数，pi与被测生物体创口处的介电特性参数（介电系数εr和电导率σ）相关，而生物体不同创口状态，其介电特性参数不同，两者满足特定的相关性。In formula (15), the denominator parametersq1 andq2 are both constants, andpi is related to the dielectric characteristic parameters (dielectric constantεr and conductivityσ ) of the wound of the measured biological body. The dielectric characteristic parameters are different for different wound states of the biological body, and the two satisfy a specific correlation.
8）由于结构对称性，只需要针对步骤7）公式(15)中复阻抗Z1、Z3的模型参数pi（i=1~16）进行主成分分析，从中提取主要参数m1、m2，参数m1、m2与pi之间满足如下关系：8) Due to the structural symmetry, it is only necessary to perform principal component analysis on the model parameterspi (i = 1~16) of the complex impedanceZ1 andZ3 in formula (15) in step 7) to extract the main parametersm1 andm2. The parametersm1 ,m2 andpi satisfy the following relationship:
其中，特征矩阵C（16×2矩阵）取值如下：Among them, the characteristic matrix C (16×2 matrix) takes the following values:
参考图8，本实施例结合生物皮肤、脂肪和肌肉组织（107、108、109）介电特性参数与创口（110）尺寸大小，对创口状态分为四类：正常M1、初创（流血）M2、凝血M3、愈合M4，并基于测量方法步骤1-5和判别方法1-3提取分类中心：M1(34.8567, 26.4264)，M2(33.4988,26.3334)，M3(33.5171,26.105)，M4(33.6126, 26.1333)。8 , this embodiment combines the dielectric property parameters of biological skin, fat and muscle tissues (107, 108, 109) with the size of the wound (110) to classify the wound status into four categories: normalM1 , initial wound (bleeding)M2 , coagulationM3 , and healingM4 , and extracts the classification center based on the measurement method steps 1-5 and the discrimination method 1-3:M1 (34.8567, 26.4264),M2 (33.4988, 26.3334),M3 (33.5171, 26.105),M4 (33.6126, 26.1333).
基于创口状态管理数据库中创口状态类别，对探头测量获取的主要参数M=(33.4985, 26.3341)进行聚类分析并判别：其到类别中心M2距离最短，故P2=1时，可判定当前创口状态为2. 初创（流血）状态。Based on the wound status categories in the wound status management database, cluster analysis is performed on the main parameters M=(33.4985, 26.3341) obtained by the probe measurement and it is determined that its distance to the category center M2 is the shortest. Therefore, whenP2 =1, the current wound status can be determined to be 2. Initial wound (bleeding) status.
需要说明的是，以上给出的实施例仅为实现本发明的示例，本发明不限于上述实施例。本领域的技术人员根据本发明技术方案的技术特征所做出的任何非本质的添加、替换，均属于本发明的保护范围。It should be noted that the above embodiments are only examples for implementing the present invention, and the present invention is not limited to the above embodiments. Any non-essential additions and substitutions made by those skilled in the art based on the technical features of the technical solution of the present invention shall fall within the protection scope of the present invention.
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