CN113243904A - Non-invasive external wound in-vivo monitoring probe and measuring method - Google Patents
Non-invasive external wound in-vivo monitoring probe and measuring method Download PDFInfo
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Abstract
The invention discloses a non-invasive external wound monitoring probe, which comprises an outer edge metal polar plate, a medium substrate and a central metal conduction band, wherein the outer edge metal polar plate is positioned on the medium substrate; through holes are respectively arranged at two ends of the metal conduction band, the metal polar plate at the outer edge and the dielectric substrate to form a coaxial feed excitation port. The invention also discloses an in-vitro wound monitoring method of the monitoring probe, which is characterized in that the probe is connected with a vector network analyzer during measurement, main parameters are extracted from the measurement parameters through a specific conversion relation and a circuit analysis model, and the wound state can be distinguished and analyzed based on the main parameters.
Description
Technical Field
The invention relates to the field of biological tissue electromagnetic detection, in particular to a biological tissue high-frequency (>1GHz) electromagnetic non-invasive wound in-vivo monitoring probe and a measuring method thereof. The invention is suitable for real-time in-vivo monitoring of the external wound state of the organism. The device is easy to conform, can be miniaturized, has higher portability and measurement accuracy, and has good application prospect.
Background
Wound healing is a very important and lengthy process for the injured. The wound is monitored, so that not only can the wound condition be known in real time and further effectively processed, but also real-time and effective information can be provided for wound evaluation and treatment plan. In addition, reliable information resources are provided for clinical research. Therefore, the wound monitoring has very important application value and research significance.
The modern medical health field is gradually changing to digitalization, networking and family. This means that medical monitoring techniques 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 techniques are primarily based on the experience of the clinical staff, assessed by 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 image techniques, represented by Optical Coherence Tomography (OCT), have good real-time performance and meet high accuracy and non-invasive requirements. However, OCT detection is susceptible to interference from external factors such as bandages, drugs, blood flow, etc., and its monitoring cost is relatively high due to the sensitivity of the optical instrument.
Disclosure of Invention
The invention aims to provide a non-invasive measuring probe capable of monitoring the condition of a wound outside a living body in real time and a corresponding measuring method. The probe has good conformal property, can be attached between bandage and other wound protection materials, prevents direct contact with a wound, realizes non-invasion, is easy to miniaturize, and has high portability and array property; the measuring method is based on the transmission line theory, can obtain a plurality of characteristic parameters in real time, and improves the accuracy of the measuring result. After the probe array is formed, the imaging effect can be realized based on the measurement parameters, and the imaging resolution is higher.
In order to realize the task, the invention adopts the following technical solution to realize:
a non-invasive external wound monitoring probe comprises a central metal conduction band, an outer edge metal polar plate and a dielectric substrate, wherein the central metal conduction band and the outer edge metal polar plate are positioned on the dielectric substrate at the same side, and a gap is reserved between the central metal conduction band and the outer edge metal polar plate;
through holes are respectively arranged at two ends of the metal conduction band, the metal polar plate at the outer edge and the dielectric substrate to form a coaxial feed excitation port.
Furthermore, the through holes penetrating through the metal conduction band, the outer edge metal polar plate and two ends of the dielectric substrate are symmetrically arranged.
The two ends of the metal conduction band and the outer edge of the metal polar plate are both arc-shaped, and the arc top of the metal conduction band and the arc tops of the two ends of the inner side of the outer edge of the metal polar plate are arranged in a concentric mode.
The medium substrate is made of a flexible circuit substrate FPC, and the metal conduction band and the outer edge metal polar plate are made of gold or surface gold-plated copper.
The invention also discloses an in-vitro wound monitoring method of the monitoring probe, which comprises the following steps:
1) selecting a monitoring probe A and a monitoring probe B;
2) placing a monitoring probe in the middle of an invasive material wrapping a wound, wherein the thickness of the invasive material between the probe and the wound is not more than 10 mm; the metal conduction band (101) surface of the monitoring probe faces the surface of the wound, and the medium substrate (103) surface of the monitoring probe is continuously coated with the wound protection material. The probe is used as a wound monitoring probe A; placing the other probe into the wound protection material wrapping the monitoring probe A, and then placing the whole probe into the air to be used as a calibration monitoring probe B;
3) the feed ends of the wound monitoring probe A and the calibration monitoring probe B are respectively connected to the vector network analyzer through coaxial cables, and the working frequency is high>1GHz, and a two-port network scattering matrix S of a calibration monitoring probe B and a wound monitoring probe A is obtained through measurement0And S1：
In the formula (1), SijThe method comprises the steps that a two-port network scattering matrix S parameter of a probe represents a transmission coefficient from a port j to a port i when other ports are matched;
4) according to the parameter S0And S1Further calculating two-port network impedance matrix Z of calibration monitoring probe B and wound monitoring probe A0And Z1The specific calculation formula is as follows:
in the formula (2), Zi ijTwo-port network impedance matrix Z for a probeiParameter, representing the transfer impedance from port j to port i, ZcThe characteristic admittance of a feed port of the probe is shown, and I is an identity matrix;
7) two-port network impedance matrix Z of wound monitoring probe A1Two-port network impedance matrix Z minus calibration monitoring probe B0Finally obtaining a calibrated two-port network impedance matrix Z of the wound monitoring probe A1-Z0A parameter;
8) establishing a T-shaped equivalent circuit model aiming at the two-port network of the wound monitoring probe A, and calibrating the two-port network impedance matrix Z of the wound monitoring probe A to Z1-Z0The parameters are processed to obtain complex impedance Z of T-shaped equivalent circuit1、Z2、Z3And satisfies the following relationship:
7) for complex impedance Z1、Z2、Z3Real and imaginary parts of, at the point of maximum resonance frequency f0Nearby constructing a frequency distribution model, wherein the complex impedance Z is1、Z2、Z3The real and imaginary parts of (c) and the operating frequency f satisfy the following relationship:
wherein q is1、q2Are all constant, pi(i 1-24) is a dielectric characteristic parameter of the wound of the tested organism;
8) for step 7) complex impedance Z1、Z2、Z3Model parameter p ofi(i 1-24) performing principal component analysis, and extracting a parameter m therefrom1、m2Parameter m1、m2And piSatisfies the following relationship:
M＝P·C＝[m1 m2]＝[p1 … p24]·C (5)
wherein the matrix C (24 × 2 matrix) is a parameter pi(i is 1-24);
11) obtaining a two-port network impedance matrix Z of the calibrated wound monitoring probe A obtained in the step 5) as Z1-Z0Constructing a wound state management database according to the parameters and the dielectric characteristic parameters of the wound of the tested organism obtained in the step 8); managing and classifying the wound states, and extracting a classification center: miIs the center of the parameter matrix of the wound state, i is the wound state category;
12) based on the opening state category in the wound state management database, a main parameter M (M) obtained by measuring the probe is1,m2]Performing cluster analysis and discrimination, when P isiAnd when the current wound state is 1, the wound state type corresponding to the i is the current wound state.
Preferably, Z in step 4)c＝50Ω。
Compared with the prior art, the non-invasive external wound in-vivo monitoring probe has the following advantages:
1. the measurement does not need to directly contact with the tissue, and the biological tissue is not damaged and does not cause cross contamination with the biological tissue.
2. The probe is made of a flexible substrate material, so that the conformal capability is high, and the measurement is less influenced by the shape of the tissue.
3. The whole probe is frivolous, and the size is less (equal to woundplast size specification), and the portability is high, and easily a plurality of probes carry out the formation of image monitoring.
4. The working frequency range of the probe is high (>1GHz), and high information resolution is easy to obtain.
Drawings
FIG. 1 is a front, back and side view of the probe construction 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. 1 a.
FIG. 2 is a front and side view of the central metal conduction band of the probe of the present invention. Wherein fig. 2a is a front view of the metal conduction band, fig. 2b is a front side view of fig. 2a, and fig. 2c is a left side view of fig. 2 a.
FIG. 3 is a front and side view of a metal plate of the probe of the present invention. In which fig. 3a is a front view of the pole plate, and fig. 3b is a left side view of fig. 3 a.
FIG. 4 is a front and side view of a 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. 4 a.
FIG. 5 is a schematic view of the via location of the probe of the present invention.
FIG. 6 is a diagram of a simulation structural model in an embodiment of the invention.
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.
FIG. 8 shows dielectric characteristics of biological tissues in an example of the present invention. Where (8a) is the permittivity of each tissue and (8b) is the conductivity of each tissue.
FIG. 9 is a graph comparing the impedance results of the probe for monitoring normal tissue and abnormal tissue under different structural designs at the two ends of the probe in the embodiment of the invention. Wherein, fig. 9a is a comparison graph of real part of impedance under the design of open circuit at two ends of the probe, fig. 9b is a comparison graph of imaginary part of impedance under the design of open circuit at two ends of the probe, fig. 9c is a comparison graph of real part of impedance under the design of rectangular closed at two ends of the probe, fig. 9d is a comparison graph of imaginary part of impedance under the design of rectangular closed at two ends of the probe, fig. 9e is a comparison graph of real part of impedance under the design of structure of the invention, and fig. 9f is a comparison graph of imaginary part of impedance under the design of structure of the invention.
The reference numerals in the drawings denote: 101. the device comprises a central metal conduction band, 102, a metal pole plate, 103, a dielectric substrate, 104, a through hole, 105, a feed coaxial line, 106, a simulation bandage, 107, simulation skin tissue, 108, simulation fat tissue, 109, simulation muscle tissue, 110 and a simulation wound.
The present invention is further described below with reference to the attached drawings, along with the principles and embodiments provided by the inventors.
Detailed Description
The working principle of the probe of the invention is as follows: due to the difference of dielectric coefficient and conductivity between the tissues of the wound part and the normal part of the organism near the probe, the phase change and amplitude loss of an electromagnetic field in the propagation process between the feed ports of the probe are different. This discrepancy can lead to differences in the transmission parameters of the instrument measuring electromagnetic field propagating between the probe feed ports. By establishing a model and extracting main analysis parameters, database information can be compared according to the parameters, and further the wound condition information of the organism can be judged.
Based on the above principle, the present embodiment provides a non-invasive external trauma in vivo monitoring probe and a measurement method, and the structure composition and the working mode thereof are as follows:
referring to fig. 1, this embodiment presents a non-invasive trauma in vivo monitoring probe. The probe mainly comprises four parts: the first part is a central metal conduction band 101, the second part is an outer edge metal polar plate 102, the third part is a dielectric substrate 103, and the fourth part is a via hole 104.
The central metal conduction band 101 and the outer edge metal plate 102 are located on the dielectric substrate 103, and a gap is left between the central metal conduction band and the outer edge metal plate 102;
through holes 104 are respectively arranged at two ends of the metal conduction band 101, the outer edge metal polar plate 102 and the dielectric substrate 103 to form a coaxial feed excitation port.
The via holes 104 penetrating through the metal conduction band 101, the outer edge metal plate 102 and the two ends of the dielectric substrate 103 are symmetrically arranged.
The two ends of the metal conduction band 101 and the outer edge of the metal pole plate 102 are both arc-shaped, and the arc top of the metal conduction band 101 and the arc tops of the two ends of the inner side of the outer edge of the metal pole plate 102 are arranged in a concentric mode. The conventional CPW transmission line structure has only a central conduction band and two side plates and does not consider the design at both ends. However, the structural design of the two ends inevitably generates energy reflection, which further affects the sensitivity of the monitoring result.
Referring to fig. 9, in order to reduce the influence of the two-end reflection on the monitoring result as much as possible. Through the comparative study of structures (two ends are open, two ends are rectangular and closed, and the structure of the invention) of different types, the invention finds that when the two ends are closed in a concentric arc form, the energy reflection can be reduced to the maximum extent, the monitoring sensitivity of the probe is improved, and the structural forms of the two ends of the probe are finally determined.
The dielectric substrate 103 is made of a flexible circuit substrate FPC (polyimide accounts for 90%), the metal conduction band 101 and the pole plate 102 are made of copper, a plating layer is arranged on the surface of the metal conduction band and the pole plate, and the plating layer is coated by gold materials. The overall dimension specification of the probe is as follows: 83.45 x 23.45 x 0.135 (length x width x thickness in mm).
Referring to FIG. 2, the distance l between the centers of the two ends of the central metal conduction band 101160mm, the center-to-center spacing l of the vias 104 on the metal conduction band 101255.92mm, width d of metal conduction band 1011Thickness h of metal conduction band 101 being 3.15mm1＝0.035mm。
Referring to fig. 3, the metal plate 102 has an internal gap width d33.45mm, width d of the metal plate 102223.45mm, the thickness of the metal plate 102 is h1＝0.035mm。
Referring to FIG. 4, the dielectric substrate 103 has a thickness h2＝0.1mm。
Referring to fig. 5, the via 104 aperture d51.3mm, via hole 104 center-to-center spacing d45.08 mm. In the monitoring probe of the embodiment, a standard SMA feed connector (SMA-KHD100) is welded at a through hole 104 to serve as a feed port of the probe, and the probe is connected with a vector network analyzer through a patch cable.
Referring to fig. 6, the monitoring probe of the present embodiment is used to monitor the wound status of external trauma (bleeding occurs), and the measurement method comprises the following steps:
1) selecting a monitoring probe A and a monitoring probe B;
2) monitoring probe A according to actual conditionsMetal conduction band 101Facing the wound site 110 and being attached between the wound site 110 of the living being and the wound dressing 106 of the wound protection material, wherein the thickness of the wound protection material wrapped between the metal conduction band 101 and the wound is 2 mm; the back of the medium substrate 103 of the probe A can be continuously coatedA wound-protecting material; the monitoring probe B is placed into the wound protection material wrapping the monitoring probe A, and then the whole is placed in the air to be used as a calibration monitoring probe B; this condition is very important and monitoring sensitivity beyond 10mm is unreliable.
3) Connecting the feed end of the probe to a vector network analyzer through a coaxial cable, wherein the working frequency is 1 GHz-6 GHz, and respectively measuring to obtain two-port network scattering matrixes S of the probes B and A0And S1：
4) According to the parameter S0And S1Further calculating two-port network impedance matrix Z of probes B and A0And Z1. The specific calculation method is as follows:
in the formula (13), ZcThe present example is given with the characteristic admittance, Z, of the feed port of the probec50 Ω. And I is an identity matrix.
5) Two-port network impedance matrix Z of wound monitoring probe A1Two-port network impedance matrix Z minus calibration probe B0Finally obtaining a calibrated two-port network impedance matrix Z ═ Z of the wound monitoring probe A1-Z0And (4) parameters.
6) Referring to FIG. 7, a "T" type equivalent circuit model is established for the two-port network of the wound monitoring probe A, the circuit consisting essentially of a complex impedance Z1、Z2、Z3The impedance matrix Z parameter of the two-port network obtained after calibration of the probe A and the impedance matrix Z parameter satisfy the following relation:
referring to fig. 6, since the wound is presented in this embodiment with structural symmetry, there are: z1＝Z2＝Z11+Z21，Z3＝Z21。
7) For complex impedance Z1、Z3Real and imaginary parts of, at the point of maximum resonance frequency f0A frequency distribution model (the frequency band is 2-3 GHz) is built near 2.6GHz, and complex impedance Z in the model1、Z3Satisfies the following relation between the real and imaginary parts of (c) and the operating frequency f:
in the formula (15), the denominator parameter q1、q2Are all constant, piAnd the dielectric characteristic parameter (dielectric coefficient epsilon) of the wound of the tested organismrAnd conductivity σ), while the dielectric property parameters of different wound states of the living body are different, and the two satisfy a specific correlation.
8) Due to the structural symmetry, only the complex impedance Z in the formula (15) for the step 7) is needed1、 Z3Model parameter p ofi(i 1-16) performing principal component analysis, and extracting a main parameter m from the principal component analysis1、 m2Parameter m1、m2And piSatisfies the following relationship:
M＝P·C＝[m1 m2]＝[p1 … p16]·C
the feature matrix C (16 × 2 matrix) takes the following values:
| 0.26 | -0.27 | 0.25 | -0.22 | -0.27 | 0.26 | 0.24 | -0.24 | -0.25 | -0.25 | 0.27 | -0.26 | -0.16 | 0.26 | -0.26 | 0.25 |
| -0.13 | -0.04 | 0.26 | -0.39 | 0.05 | 0.03 | -0.28 | 0.31 | -0.22 | 0.24 | 0.03 | -0.10 | 0.58 | -0.12 | -0.19 | 0.27 |
referring to fig. 8, the present embodiment combines the dielectric property parameters of biological skin, fat and muscle tissues (107, 108, 109) and the size of the wound (110), and is classified into four categories for the wound status: normal M1First wound (bleeding) M2Blood coagulation M3Healing M4And extracting a 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)。
Based on the opening state category in the wound state management database, performing cluster analysis and discrimination on the main parameters M (33.4985,26.3341) obtained by probe measurement: it goes to the class center M2The shortest distance, so P2When 1, the current wound state can be determined to be 2, the initial wound (bleeding) state.
It should be noted that the above-mentioned embodiments are only examples for implementing the present invention, and the present invention is not limited to the above-mentioned embodiments. Any non-essential addition and replacement made by the technical characteristics of the technical scheme of the invention by a person skilled in the art belong to the protection scope of the invention.
Claims (6)
1. A non-invasive external wound monitoring probe comprises a central metal conduction band (101), an outer edge metal polar plate (102) and a dielectric substrate (103), and is characterized in that: the central metal conduction band (101) and the outer edge metal pole plate (102) are positioned on the dielectric substrate (103) at the same side, and a gap is reserved between the central metal conduction band (101) and the outer edge metal pole plate (102);
through holes (104) are respectively formed through the metal conduction band (101), the outer edge metal polar plate (102) and the two ends of the dielectric substrate (103) to form a coaxial feed excitation port.
2. The non-invasive in vitro wound monitoring probe according to claim 1, wherein: the through holes (104) penetrating through the metal conduction band (101), the outer edge metal polar plate (102) and the two ends of the dielectric substrate (103) are symmetrically arranged.
3. The non-invasive in vitro wound monitoring probe according to claim 1, wherein: the two ends of the metal conduction band (101) and the two ends of the outer edge metal pole plate (102) are both arc-shaped, and the arc top of the metal conduction band (101) and the arc tops of the two ends of the inner side of the outer edge metal pole plate (102) are arranged in a concentric circle mode.
4. The non-invasive in vitro wound monitoring probe according to claim 1, wherein: the dielectric substrate (103) is made of a flexible circuit substrate FPC, and the metal conduction band (101) and the outer edge metal polar plate (102) are made of gold or copper with gold-plated surface.
5. An in vitro wound monitoring method using the monitoring probe of any one of claims 1 to 4, characterized in that: the method comprises the following steps:
1) selecting a monitoring probe A and a monitoring probe B;
2) placing a monitoring probe in the middle of an invasive material wrapping a wound, wherein the thickness of the invasive material between the probe and the wound is not more than 10 mm; the metal conduction band (101) surface of the monitoring probe faces the surface of the wound, the medium substrate (103) surface of the monitoring probe is continuously coated with the wound protection material, and the monitoring probe is used as a wound monitoring probe A; placing the other probe into the wound protection material wrapping the monitoring probe A, and then placing the whole probe into the air to be used as a calibration monitoring probe B;
3) respectively connecting the feed ends of the wound monitoring probe A and the calibration monitoring probe B to the vector network through coaxial cablesOn the analyzer, operating frequency>1GHz, and a two-port network scattering matrix S of a calibration monitoring probe B and a wound monitoring probe A is obtained through measurement0And S1：
In the formula (1), SijThe method comprises the steps that a two-port network scattering matrix S parameter of a probe represents a transmission coefficient from a port j to a port i when other ports are matched;
4) according to the parameter S0And S1Further calculating two-port network impedance matrix Z of calibration monitoring probe B and wound monitoring probe A0And Z1The specific calculation formula is as follows:
in the formula (2), Zi ijTwo-port network impedance matrix Z for a probeiParameter, representing the transfer impedance from port j to port i, ZcThe characteristic admittance of a feed port of the probe is shown, and I is an identity matrix;
5) two-port network impedance matrix Z of wound monitoring probe A1Two-port network impedance matrix Z minus calibration monitoring probe B0Finally obtaining a calibrated two-port network impedance matrix Z of the wound monitoring probe A1-Z0A parameter;
6) establishing a T-shaped equivalent circuit model aiming at the two-port network of the wound monitoring probe A, and calibrating the two-port network impedance matrix Z of the wound monitoring probe A to Z1-Z0The parameters are processed to obtain complex impedance Z of T-shaped equivalent circuit1、Z2、Z3And satisfies the following relationship:
7) for complex impedance Z1、Z2、Z3Real and imaginary parts of, at the point of maximum resonance frequency f0Nearby constructing frequency distribution model, complex impedance Z in the model1、Z2、Z3Satisfies the following relation between the real and imaginary parts of (c) and the operating frequency f:
wherein q is1、q2Are all constant, pi(i is 1-24) is a dielectric property parameter of the wound of the tested organism;
8) for step 7) complex impedance Z1、Z2、Z3Model parameter p ofi(i 1-24) performing principal component analysis, and extracting a parameter m therefrom1、m2Parameter m1、m2And piSatisfies the following relationship:
M＝P·C＝[m1 m2]＝[p1 … p24]·C (5)
wherein the matrix C (24 × 2 matrix) is a parameter pi(i is 1-24);
9) obtaining a two-port network impedance matrix Z of the calibrated wound monitoring probe A obtained in the step 5) as Z1-Z0Constructing a wound state management database according to the parameters and the dielectric characteristic parameters of the wound of the tested organism obtained in the step 8); managing and classifying the wound states, and extracting a classification center: miIs the center of the parameter matrix of the wound state, i is the wound state category;
10) based on the opening state category in the wound state management database, the main parameter M ═ M obtained by measuring the probe1,m2]Performing cluster analysis and discriminationPiAnd when the current wound state is 1, the wound state type corresponding to the i is the current wound state.
6. The method for monitoring trauma in vitro of a monitoring probe according to claim 5, wherein: z in the step 4)c＝50Ω。
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