Resistance impedance detection probe control method, device and system

Abstract

The invention relates to the field of electrical impedance detection, in particular to a resistance impedance detection probe control method, device and system, and the method comprises the steps: detecting the liquid state characteristics of the environment where a resistance impedance detection probe is located, so as to estimate the liquid ion flowing space distribution information of the surface of the probe; estimating a bioelectricity signal drift change characteristic formed by liquid ions in a detection coverage range corresponding to the electrode, and adjusting an electric signal detection parameter of the electrode; adjusting signal processing parameters of signal processing ends corresponding to the electrodes on the basis of change characteristics of bioelectricity signal queues acquired by all the electrodes on the surface of the probe; and based on the resistance impedance information generated by the signal processing end and the position change information of all the electrodes on the surface of the probe in the environment, a resistance impedance distribution image is generated, so that a resistance impedance abnormal area in the environment is determined. The working state of the probe can be adjusted in the changing process of the liquid environment in the human tissue, and therefore the bio-electricity signal of the liquid environment is accurately detected.

Description

Technical Field

[0001] The present invention relates to the field of electrical impedance detection, and in particular to a method, device and system for controlling a resistance impedance detection probe. Background Art

[0002] Resistance impedance is commonly found in objects. For human tissue, the resistance impedance inside human tissue is related to the tissue structure and type. When human tissue is in a healthy state, the corresponding resistance impedance and the resistance impedance of other surrounding tissues basically show a uniform or smooth change; when human tissue has lesions such as tumors, the corresponding resistance impedance will be significantly different from the resistance impedance of other surrounding tissues without lesions. Therefore, by performing resistance impedance detection on human tissue, a reliable basis can be provided for identifying the lesions inside human tissue, which is widely used in the detection of spinal tumor lesions.

[0003] Considering the shape and structure characteristics of human tissues such as the spine, the existing technology uses a resistance impedance detection probe to penetrate into the spine, and uses multiple electrodes on the probe surface to detect the bioelectric signal detection of the body fluid environment inside the spine, and analyzes the bioelectric signal to obtain the resistance impedance distribution of the body fluid environment inside the spine. It is precisely because multiple electrodes are distributed on the probe surface that the bioelectric signals of different areas of the body fluid environment inside the spine can be obtained during a single detection process. The bioelectric signal is formed by the combined effect of the flow of ions in the body fluid and the resistance impedance of the biological tissue inside the spine. The greater the ion flow rate or the greater the resistance impedance, the stronger the bioelectric signal. In actual detection, affected by factors such as the flow state of the body fluid inside the spine and the infiltration state of the body fluid on the probe surface, some electrodes on the probe surface may not be able to form a good contact with the body fluid or cannot accurately detect the changes in the bioelectric signal of the body fluid environment in a timely manner, and cannot form an accurate and reliable detection of the global range inside the spine. Therefore, how to adjust the working state of the probe during the change of the liquid environment inside the human tissue, and expect to accurately detect the bioelectric signal of the liquid environment, is of great significance to improving the resistance impedance detection accuracy and credibility of the probe. Summary of the invention

[0004] In order to avoid the situation that the probe surface electrodes cannot form good contact with the liquid or cannot timely and accurately detect the changes in the bioelectrical signals of the liquid environment, and thus cannot ensure the resistance impedance detection accuracy and reliability of the probe, the present invention provides a resistance impedance detection probe control method, the method comprising the following steps: S1: Detecting the environment where the resistance impedance detection probe is located to obtain liquid state characteristics of the environment; S2: estimating the spatial distribution information of the liquid ion flow on the probe surface based on the liquid state characteristics; S3: based on the spatial distribution information of the liquid ion flow, estimating the drift change characteristics of the bioelectric signal formed by the liquid ions in the detection coverage range corresponding to each of the electrodes on the probe surface; based on the drift change characteristics of the bioelectric signal, adjusting the electrical signal detection parameters of each of the electrodes on the probe surface; S4: adjusting the signal processing parameters of the signal processing terminals corresponding to all the electrodes based on the change characteristics of the bioelectric signal queues collected by all the electrodes on the surface of the probe; S5: generating a resistance impedance distribution image inside the environment based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface in the environment; S6: Based on the resistance impedance distribution image, determine the resistance impedance abnormal area inside the environment.

[0005] Preferably, in step S1, specifically: Dynamically detect the liquid in the environment where the resistance impedance detection probe is located to obtain the variation characteristics of the size of the infiltration range of the liquid on the probe surface and the spatial variation characteristics of the flow speed of the liquid; In step S2, specifically: Based on the variation characteristics of the size of the infiltration range and the distribution range characteristics of the electrodes on the probe surface, estimating the range information of the effective excitation of the electrodes on the probe surface by the liquid in the environment; Based on the spatial variation characteristics of the flow velocity and the range information of the effective excitation of the electrode on the probe surface by the liquid, the spatial distribution information of the liquid ion flow on the probe surface in the environment is estimated; wherein the spatial distribution information of the liquid ion flow includes the size distribution information of the liquid ion flow migration rate at different positions of the probe surface in the environment.

[0006] Preferably, in step S3, specifically: Based on the spatial distribution information of the liquid ion flow, the spatial distribution information of the bioelectric current intensity formed by the liquid ions on the probe surface is estimated; based on the spatial distribution information of the bioelectric current intensity and the detection coverage range corresponding to all the electrodes on the probe surface, the drift change characteristics of the bioelectric signal generated by all the electrodes are estimated; wherein the bioelectric signal drift change characteristics are the time domain change characteristics of the bioelectric signal intensity fluctuation formed by the liquid ion flow migration in the detection coverage range of the electrode; Based on the bioelectric signal drift change characteristics, the bioelectric signal intensity fluctuation change frequency and the bioelectric signal intensity fluctuation change difference corresponding to the detection coverage range of the electrode are obtained; based on the bioelectric signal intensity fluctuation change frequency and the bioelectric signal intensity fluctuation change difference, the electrical signal detection frequency and the electrical signal detection sensitivity of the electrode are adjusted respectively; In step S4, specifically: Perform frequency domain analysis on the bioelectric signal queues collected by all electrodes on the probe surface to obtain signal frequency size distribution information of the bioelectric signal queues collected by the electrodes; estimate the frequency domain range of the noise component of the bioelectric signal queue based on the signal frequency size distribution information; and adjust the signal noise reduction filter processing parameters of the signal processing end corresponding to the electrode based on the noise component frequency domain range.

[0007] Preferably, in step S5, specifically: Acquire spatial posture change information of the probe in the environment, and determine position change information of all electrodes on the probe surface in the environment based on the spatial posture change information and the distribution position information of all electrodes on the probe surface; Based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface in the environment, a resistance impedance distribution sub-image of a corresponding subspace inside the environment obtained by the probe corresponding to each spatial posture detection when the probe is located in the environment with several different spatial postures is generated, and all resistance impedance distribution sub-images are integrated into a resistance impedance distribution image of the global scope inside the environment; In step S6, specifically: The resistance impedance distribution image is subjected to the recognition of the spatial variation of the impedance value, and the region with abnormal impedance variation rate in the global range within the environment is determined as the resistance impedance abnormal region within the environment.

[0008] On the other hand, the present invention provides a resistance impedance detection probe control device, which is used to implement the resistance impedance detection probe control method as described above, and the resistance impedance detection probe control device includes the following modules: An environment detection module, used to implement the above step S1; A liquid ion flow estimation module, used to implement the above step S2; An electrode electrical signal detection and adjustment module, used to implement the above step S3; A signal processing parameter adjustment module, used to implement the above step S4; A resistance impedance distribution identification module, used to implement the above step S5; The resistance impedance abnormal area positioning module is used to implement the above step S6.

[0009] In addition, the present invention also provides a resistance impedance detection probe control system, the system comprising: The above-mentioned resistance impedance detection probe control device; A visualization display device is used to generate a visualization image of the impedance change rate abnormal area in the global range inside the environment according to the impedance change rate abnormal area determined by the resistance impedance detection probe control device.

[0010] Compared with the prior art, the present invention has the following beneficial effects: The environment in which the resistance impedance detection probe is located is detected to obtain the liquid state characteristics of the environment; based on the liquid state characteristics, the spatial distribution information of the liquid ion flow on the probe surface is estimated. There are multiple electrodes distributed on the surface of the resistance impedance detection probe. When the probe is inserted into human tissues such as the spine, the probe will be immersed in the body fluid environment inside the human tissue. The ion flow migration state in the body fluid environment directly affects the detection state and detection results of the bioelectric signals of the body fluid environment by the electrodes on the probe surface. If some electrodes on the probe surface are not immersed in the body fluid environment, the probe will not be able to fully collect the bioelectric signals inside the body fluid environment. In addition, there are differences in the ion flow migration state in different areas of the body fluid environment, and the detection sensitivity of the probe surface electrodes themselves directly affects the reliability of the electrodes collecting bioelectric signals. In order to ensure that the electrodes on the probe surface can adapt to the ion flow migration state in different areas of the body fluid environment for accurate and efficient detection and collection, it is necessary to pre-detect the liquid state characteristics of the environment in which the probe is located, so as to estimate the liquid flow spatial distribution information at different positions on the probe surface in the environment, so that the electrodes at different positions on the probe surface can collect bioelectric signals in a matching mode, and maximize the reliability of the collection of bioelectric signals of all electrodes on the probe surface.

[0011] Based on the spatial distribution information of liquid ion flow, estimate the drift change characteristics of the bioelectric signal formed by the liquid ions in the detection coverage range corresponding to each of the electrodes on the probe surface; based on the drift change characteristics of the bioelectric signal, adjust the electrical signal detection parameters of each of the electrodes on the probe surface. After the probe is immersed in the body fluid environment inside the human body, the flow of liquid ions in the body fluid environment area directly contacted by the electrodes at different positions on the probe surface is not the same. If all the electrodes on the probe surface use the same mode to collect bioelectric signals, it will not be possible to ensure that the collected bioelectric signals truly reflect the size of the bioelectric signals in the body fluid environment area that they are in direct contact with. In addition, all electrodes on the probe surface correspond to specific detection coverage ranges, resulting in different changes in bioelectric signal intensity in the detection coverage range corresponding to each electrode due to the flow of liquid ions. The bioelectric signal intensity fluctuations in the detection coverage range corresponding to some electrodes are faster, while the bioelectric signal intensity fluctuations in the detection coverage range corresponding to another electrode are slower. There are also some electrodes with larger differences in the fluctuations in the intensity of bioelectric signals in the detection coverage range corresponding to other electrodes, while there are other electrodes with smaller differences in the fluctuations in the pressure of bioelectric signals in the detection coverage range corresponding to other electrodes. If all electrodes on the probe surface use the same detection frequency and detection sensitivity to collect bioelectric signals in their corresponding detection coverage ranges, it may lead to problems such as missing or incorrect detection of bioelectric signals. For this reason, based on the spatial distribution information of the flow of liquid ions in the body fluid environment, the drift change characteristics of bioelectric signals formed in the detection coverage ranges corresponding to all electrodes on the probe surface due to the flow and migration of liquid ions are estimated, and the electrical signal detection parameters of all electrodes on the probe surface are adjusted to ensure that each electrode can collect bioelectric signals in a matching electrical signal detection mode, thereby improving the detection accuracy of bioelectric signals.

[0012] Based on the changing characteristics of the bioelectric signal queues collected by all electrodes on the probe surface, the signal processing parameters of the signal processing ends corresponding to all electrodes are adjusted. All electrodes on the probe surface are connected to a signal processing end, which is used to process the bioelectric signals collected by each electrode to obtain resistance impedance information. In view of the fact that the signal-to-noise ratio of the bioelectric signals collected by different electrodes in their own detection coverage range is not the same, the noise reduction filtering processing mode required to be implemented before the bioelectric signal calculation is converted into resistance impedance information is also different accordingly. In order to accurately perform noise reduction filtering on the bioelectric signals collected by all electrodes on the probe surface, the signal frequency size distribution of the bioelectric signal queue collected by each electrode in the corresponding time period is first identified to obtain the frequency size of all signal components under the bioelectric signal queue, so as to estimate the frequency domain range of the noise component of the bioelectric signal queue, so as to adjust the signal noise reduction filtering processing parameters of the corresponding signal processing end in a targeted manner, so as to ensure that the bioelectric signal generated by each electrode can be effectively noise-reduced and filtered, and improve the accuracy of the subsequent calculation of the bioelectric signal into resistance impedance information.

[0013] Based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface in the environment, a resistance impedance distribution image inside the environment is generated; based on the resistance impedance distribution image, the resistance impedance abnormal area inside the environment is determined. Limited by the small size of the probe itself, setting multiple electrodes on the probe surface cannot guarantee the global range of bioelectric signal collection in the body fluid environment inside the human tissue. Therefore, in the actual detection operation, it is necessary to change the spatial posture angle of the probe in the body fluid environment after it is inserted into the human tissue, so as to collect bioelectric signals from different areas in the body fluid environment. Whenever the probe switches to a spatial posture angle in the body fluid environment, the bioelectric signals collected by all electrodes on the probe surface are collected, and combined with the position information of all electrodes on the probe surface in the body fluid environment, a resistance impedance distribution sub-image of the corresponding subspace inside the body fluid environment is generated. Then, the resistance impedance distribution sub-images corresponding to the probe at different spatial posture angles are integrated into a global range of resistance impedance distribution images in the body fluid environment, so as to accurately and comprehensively characterize the distribution of the resistance impedance size of the human tissue as a whole. As mentioned earlier, when there are lesions such as tumors in human tissue, there is a large difference in the resistance impedance of the lesion area and the resistance impedance of the non-lesion area. By identifying the spatial changes in the impedance value of the resistance impedance distribution image, the abnormal impedance change area of ​​the global body fluid environment of the human tissue is determined, thereby providing a reliable basis for identifying the internal lesions of the human tissue. BRIEF DESCRIPTION OF THE DRAWINGS

[0014] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the following briefly introduces the drawings required for describing the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work. Among them: Figure 1 The present invention provides a flow chart of a resistance impedance detection probe control method.

[0015] Figure 2 It is a structural diagram of a resistance impedance detection probe control device provided by the present invention.

[0016] Figure 3 It is a structural diagram of a resistance impedance detection probe control system provided by the present invention. DETAILED DESCRIPTION

[0017] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the specific implementation methods of the present invention are described in detail below in conjunction with the accompanying drawings. It is understood that the specific embodiments described herein are only used to explain the present invention, rather than to limit the present invention. It should also be noted that, for ease of description, only the parts related to the present invention rather than all structures are shown in the accompanying drawings. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of the present invention.

[0018] The terms "including" and "having" and any variations thereof in the present invention are intended to cover non-exclusive inclusions. For example, a process, method, system, product or device comprising a series of steps or units is not limited to the listed steps or units, but may optionally include steps or units not listed, or may optionally include other steps or units inherent to these processes, methods, products or devices.

[0019] Reference to "embodiments" herein means that a particular feature, structure, or characteristic described in conjunction with the embodiments may be included in at least one embodiment of the present invention. The appearance of the phrase in various places in the specification does not necessarily refer to the same embodiment, nor is it an independent or alternative embodiment that is mutually exclusive with other embodiments. It is explicitly and implicitly understood by those skilled in the art that the embodiments described herein may be combined with other embodiments.

[0020] See also Figure 1 As shown, the present invention provides a resistance impedance detection probe control method, the method comprising the following steps: S1: Detect the environment where the resistance impedance detection probe is located to obtain the liquid state characteristics of the environment; S2: Estimate the spatial distribution information of liquid ion flow on the probe surface based on the liquid state characteristics.

[0021] Furthermore, in step S1, specifically: Dynamic detection is performed on the liquid in the environment where the resistance impedance detection probe is located to obtain the variation characteristics of the size of the liquid's infiltration range on the probe surface and the spatial variation characteristics of the liquid's flow velocity.

[0022] Furthermore, in step S2, specifically: Based on the variation characteristics of the size of the infiltration range and the distribution range characteristics of the electrodes on the probe surface, the range information of the effective excitation of the electrodes on the probe surface by the liquid in the environment is estimated; Based on the spatial variation characteristics of the flow velocity and the range information of effective excitation of the electrodes on the probe surface by the liquid, the spatial distribution information of the liquid ion flow on the probe surface in the environment is estimated; wherein the spatial distribution information of the liquid ion flow includes the size distribution information of the liquid ion flow migration rate at different positions of the probe surface in the environment.

[0023] Human tissues such as the spine contain flowable body fluids. During the flow of body fluids, the ions inside the body fluids will also flow accordingly, thus forming bioelectric signals (such as biovoltage signals or biocurrent signals). The strength of the bioelectric signals is related to the resistance impedance of human tissues. By detecting and collecting the bioelectric signals of the body fluid environment inside human tissues, the resistance impedance distribution of the body fluid environment inside human tissues can be calculated and determined. This does not require additional application of excitation voltage or excitation current to the body fluid environment inside human tissues. The bioelectric signals therein can be directly detected, reducing the complexity of probe detection. The resistance impedance detection probe mainly includes a probe carrier and a plurality of electrodes evenly distributed on the surface of the probe carrier; wherein, the probe carrier can have a slender shape structure, which is convenient for the probe carrier to pierce and insert into the human tissue; the probe carrier can be made of ceramic material, so as to have good barrier effect and biocompatibility; the electrodes can be made of highly conductive silver or other metals, and each electrode is connected to the signal processing end through a signal line, so that the bioelectric signals collected by the electrodes can be directly transmitted to the signal processing end for calculation and processing; the signal processing end can be, but is not limited to, an FPGA control board designed based on the Gowin Semiconductor GW1NR-9 FPGA chip.

[0024] When the probe is inserted into human tissues such as the spine, the probe will be immersed in the body fluid environment inside the human tissue. The ion flow migration state in the body fluid environment directly affects the detection state and detection results of the bioelectric signals of the body fluid environment by the probe surface electrodes. If some electrodes on the probe surface are not immersed in the body fluid environment, the probe will not be able to fully collect the bioelectric signals inside the body fluid environment. In addition, there are differences in the ion flow migration state in different areas of the body fluid environment, and the detection sensitivity of the probe surface electrodes themselves directly affects the reliability of the electrodes in collecting bioelectric signals. It can be seen that the immersion state of the probe in the body fluid environment and the ion flow migration speed in the body fluid environment directly affect the bioelectric signal collection state of the electrode. In order to accurately detect the immersion state of the probe in the body fluid environment and the body fluid flow speed in the body fluid environment, multiple pressure sensors and multiple flow rate sensors can be evenly arranged on the surface of the probe carrier, and all pressure sensors and the flow rate sensors are regularly arranged with all electrodes. After the probe is immersed in the body fluid environment, it is subjected to the strong effect of the body fluid. The pressure on the area of ​​the probe surface immersed in the body fluid will increase significantly. By analyzing the pressure data collected by all the pressure sensors, the range of the probe surface immersed in the body fluid can be determined, and the electrodes located in the range of the probe surface immersed in the body fluid will be affected by the ions inside the body fluid and detect the bioelectric signal. When the body fluid flow rate in the body fluid environment is greater, the ion flow rate in the body fluid is also greater, and the corresponding bioelectric signal is also stronger. However, the body fluid flow rate in the body fluid environment is not uniform, and there are differences in the body fluid flow rate in different areas of the body fluid environment. In order to enable the electrode to detect the bioelectric signal formed in the body fluid environment area where it is located in the best state, it is necessary to determine the spatial distribution information of the liquid ion flow on the probe surface, that is, the body fluid ion flow migration size distribution information at different positions on the probe surface in the body fluid environment, to provide a reliable basis for the subsequent adjustment of the bioelectric signal detection parameters of different electrodes on the probe surface.

[0025] Specifically, the body fluid in the body fluid environment where the probe is located is dynamically detected by the pressure sensor and flow rate sensor on the probe surface to obtain the pressure distribution data applied by the body fluid on the probe surface and the flow rate distribution data of the body fluid on the probe surface; then the pressure distribution data and the flow rate distribution data are analyzed to obtain the characteristics of the change in the area size of the infiltration range of the body fluid on the probe surface and the spatial change characteristics of the flow velocity. Combined with the characteristics of the change in the area size of the infiltration range of the probe surface and the characteristics of the electrode distribution range on the probe surface, the range information of the effective excitation of the electrodes on the probe surface by the body fluid in the body fluid environment is estimated; for example, based on the characteristics of the change in the area size of the infiltration range of the probe surface and the characteristics of the electrode distribution range on the probe surface, the surface area ratio of each electrode infiltrated by the body fluid is determined. If the surface area ratio exceeds the preset ratio threshold, it is determined that the electrode can be effectively excited by the body fluid, and the surface range occupied by all electrodes effectively excited by the body fluid on the probe surface is determined as the effective excitation range of the probe surface. Through the above analysis, it can be seen that the flow of body fluid drives the flow of ions inside it to form bioelectric signals, and the flow speed of body fluid in different areas of the body fluid environment is different, which provides a basis for the subsequent precise adjustment of the electrode detection method of bioelectric signals. To this end, based on the spatial variation characteristics of the flow velocity and the range information of the effective excitation of the electrodes on the probe surface by the body fluid, the size distribution information of the flow migration rate of liquid ions at different positions on the probe surface in the body fluid environment is estimated.

[0026] S3: Based on the spatial distribution information of the liquid ion flow, estimate the drift change characteristics of the bioelectric signal formed by the liquid ions in the detection coverage range corresponding to each of the electrodes on the probe surface; based on the drift change characteristics of the bioelectric signal, adjust the electrical signal detection parameters of each of the electrodes on the probe surface; S4: Based on the change characteristics of the bioelectric signal queues collected by all electrodes on the probe surface, the signal processing parameters of the signal processing terminals corresponding to all electrodes are adjusted.

[0027] Furthermore, in step S3, specifically: Based on the spatial distribution information of liquid ion flow, the spatial distribution information of the bioelectric current intensity formed by the liquid ions on the probe surface is estimated; based on the spatial distribution information of the bioelectric current intensity and the detection coverage range corresponding to all electrodes on the probe surface, the drift change characteristics of the bioelectric signal generated by all electrodes are estimated; wherein the bioelectric signal drift change characteristics are the time domain change characteristics of the bioelectric signal intensity fluctuation formed by the liquid ion flow migration in the detection coverage range of the electrode; Based on the bioelectric signal drift change characteristics, the bioelectric signal intensity fluctuation change frequency and the bioelectric signal intensity fluctuation change difference corresponding to the electrode's detection coverage range are obtained; based on the bioelectric signal intensity fluctuation change frequency and the bioelectric signal intensity fluctuation change difference, the electrode's electrical signal detection frequency and electrical signal detection sensitivity are adjusted respectively.

[0028] After the probe is immersed in the body fluid environment inside the human body, the flow of liquid ions in the body fluid environment area directly contacted by electrodes at different positions on the probe surface is different. If all electrodes on the probe surface use the same mode to collect bioelectric signals, it will not be guaranteed that the collected bioelectric signals truly reflect the size of the bioelectric signals in the body fluid environment area directly contacted by itself. In addition, all electrodes on the probe surface each correspond to a specific detection coverage range, resulting in different changes in the intensity of bioelectric signals formed in the detection coverage range corresponding to each electrode due to the flow of liquid ions. The intensity fluctuation of bioelectric signals in the detection coverage range corresponding to one part of the electrodes changes faster, while the intensity fluctuation of bioelectric signals in the detection coverage range corresponding to another part of the electrodes changes slower. There are also some electrodes that have a large difference in the intensity fluctuation of bioelectric signals in the detection coverage range corresponding to a large part of the electrodes, while the pressure fluctuation of bioelectric signals in the detection coverage range corresponding to another part of the electrodes is small. If all electrodes on the probe surface use the same detection frequency and detection sensitivity to collect bioelectric signals in the detection coverage range corresponding to themselves, it may lead to problems such as missing or wrong detection of bioelectric signals.

[0029] To this end, based on the spatial distribution information of the flow of liquid ions in the body fluid environment, the drift change characteristics of the bioelectric signal formed by the flow and migration of liquid ions in the detection coverage range corresponding to each of the electrodes on the probe surface are estimated, and the electrical signal detection parameters of each of the electrodes on the probe surface are adjusted to ensure that each electrode can collect bioelectric signals in a matching electrical signal detection mode, thereby improving the detection accuracy of bioelectric signals. Specifically, based on the fluctuation change frequency of the bioelectric signal intensity, it is determined whether the fluctuation change frequency of the bioelectric signal intensity corresponding to the detection coverage range of the electrode is higher than the current electrical signal detection frequency of the electrode; if so, the electrical signal detection frequency of the electrode is increased; if not, the electrical signal detection frequency of the electrode is kept unchanged. Based on the drift change characteristics of the bioelectric signal, it is determined whether the fluctuation change difference of the bioelectric signal intensity corresponding to the detection coverage range of the electrode is less than the electrical signal detection sensitivity of the electrode; if so, the electrical signal detection sensitivity of the electrode is increased; if not, the electrical signal detection sensitivity of the electrode is kept unchanged. In the above manner, it is possible to ensure that the electrodes on the probe surface collect their own bioelectric signals in the detection coverage range corresponding to the body fluid environment with appropriate electrical signal detection frequency and electrical signal detection sensitivity.

[0030] Furthermore, in step S4, specifically: Frequency domain analysis is performed on the bioelectric signal queues collected by all electrodes on the probe surface to obtain the signal frequency distribution information of the bioelectric signal queues collected by the electrodes; based on the signal frequency distribution information, the frequency domain range of the noise component of the bioelectric signal queue is estimated; based on the frequency domain range of the noise component, the signal noise reduction filter processing parameters of the signal processing end corresponding to the electrode are adjusted.

[0031] Given that the signal-to-noise ratios of bioelectric signals collected by different electrodes within their own detection coverage range are not the same, the noise reduction filtering processing modes required to be implemented before converting the bioelectric signals into resistance impedance information are also different. In order to accurately perform noise reduction filtering on the bioelectric signals collected by all electrodes on the probe surface, the signal frequency distribution of the bioelectric signal queue collected by each electrode in the corresponding time period is first identified to obtain the frequency size of all signal components under the bioelectric signal queue, thereby estimating the frequency domain range of the noise component of the bioelectric signal queue, and then specifically adjusting the signal noise reduction filtering processing parameters of the corresponding signal processing end, such as the frequency threshold range of the signal noise reduction filtering processing, to ensure that the bioelectric signals generated by each electrode can be effectively noise-reduced and filtered, thereby improving the accuracy of the subsequent conversion of bioelectric signal calculations into resistance impedance information.

[0032] S5: generating a resistance impedance distribution image inside the environment based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface in the environment; S6: Based on the resistance impedance distribution image, determine the resistance impedance abnormal area inside the environment.

[0033] Furthermore, in step S5, specifically: Acquire spatial posture change information of the probe in the environment, and determine position change information of all electrodes on the probe surface in the environment based on the spatial posture change information and the distribution position information of all electrodes on the probe surface; Based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface in the environment, a resistance impedance distribution sub-image of the corresponding subspace inside the environment corresponding to each spatial posture detection of the probe is generated when the probe is located in the environment in several different spatial postures, and all the resistance impedance distribution sub-images are integrated into a resistance impedance distribution image of the global scope inside the environment.

[0034] Furthermore, in step S6, specifically: The spatial variation of impedance value is identified in the resistance impedance distribution image, and the abnormal area of ​​impedance change rate in the global scope inside the environment is determined, which is used as the abnormal resistance impedance area inside the environment.

[0035] Due to the small size of the probe itself, multiple electrodes on the probe surface cannot guarantee the global range of bioelectric signal collection in the body fluid environment inside the human tissue. Therefore, in the actual detection operation, it is necessary to change the spatial posture angle of the probe in the body fluid environment after it is inserted into the human tissue, so as to collect bioelectric signals from different areas in the body fluid environment. Whenever the probe switches to a spatial posture angle in the body fluid environment, the bioelectric signals collected by all electrodes on the probe surface are collected, and the resistance impedance distribution sub-image of the corresponding subspace inside the body fluid environment is generated by combining the position information of all electrodes on the probe surface in the body fluid environment. Then, the resistance impedance distribution sub-images corresponding to the probe at different spatial posture angles are integrated into the global range of the resistance impedance distribution image in the body fluid environment, so as to accurately and comprehensively characterize the overall resistance impedance size distribution of the human tissue. As mentioned above, when there are lesions such as tumors in human tissue, there is a large difference between the resistance impedance of the lesion area and the resistance impedance of the non-lesion area. By identifying the spatial change of the impedance value of the resistance impedance distribution image, the abnormal impedance change area of ​​the global range of the body fluid environment of the human tissue is determined, thereby providing a reliable basis for identifying the lesions inside the human tissue.

[0036] See also Figure 2 As shown, the present invention provides a resistance impedance detection probe control device, which is used to implement the above-mentioned resistance impedance detection probe control method, and the device includes the following modules: An environment detection module, used to implement the above step S1; A liquid ion flow estimation module, used to implement the above step S2; An electrode electrical signal detection and adjustment module, used to implement the above step S3; A signal processing parameter adjustment module, used to implement the above step S4; A resistance impedance distribution identification module, used to implement the above step S5; The resistance impedance abnormal area positioning module is used to implement the above step S6.

[0037] The operation and effect of the resistance impedance detection probe control device of the present invention are corresponding to and consistent with the above-mentioned resistance impedance detection probe control method, and the resistance impedance detection probe control device will not be repeatedly described here.

[0038] See also Figure 3 As shown, the present invention provides a resistance impedance detection probe control system, the system comprising: The above-mentioned resistance impedance detection probe control device; A visualization display device is used to generate a visualization image of the impedance change rate abnormal area in the global range inside the environment according to the impedance change rate abnormal area determined by the resistance impedance detection probe control device.

[0039] In the above-mentioned resistance impedance detection probe control system, the visualization display device may be but is not limited to a flat display device or a three-dimensional display device, etc., so that the visualization display device can generate a visualization image of the abnormal impedance change rate area in the global range of the body fluid environment of the human tissue based on the abnormal impedance change rate area from the resistance impedance detection probe control device, thereby preliminarily locating the area where the lesion may occur inside the human tissue, and providing a reliable basis for subsequent diagnosis and treatment.

[0040] Through the description of the above embodiments, those skilled in the art can clearly understand that each embodiment can be implemented by adding a necessary general hardware platform, and of course can also be implemented by combining hardware and software. Based on such an understanding, the above technical solution can essentially or in other words be embodied in the form of a computer product, and the present invention can be implemented in the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program codes.

[0041] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it, and other embodiments may also be used. Although the present invention has been described in detail with reference to the aforementioned embodiments, ordinary technicians in this field should understand that they can still modify the technical solutions recorded in the aforementioned embodiments, or replace some of the technical features therein with equivalents. However, these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. A resistance impedance detection probe control method, characterized in that: The method comprises the following steps: S1: Detecting the environment where the resistance impedance detection probe is located to obtain liquid state characteristics of the environment; S2: estimating the spatial distribution information of the liquid ion flow on the probe surface based on the liquid state characteristics; S3: based on the spatial distribution information of the liquid ion flow, estimating the drift change characteristics of the bioelectric signal formed by the liquid ions in the detection coverage range corresponding to each of the electrodes on the probe surface; based on the drift change characteristics of the bioelectric signal, adjusting the electrical signal detection parameters of each of the electrodes on the probe surface; S4: adjusting the signal processing parameters of the signal processing terminals corresponding to all the electrodes based on the change characteristics of the bioelectric signal queues collected by all the electrodes on the surface of the probe; S5: generating a resistance impedance distribution image inside the environment based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface in the environment; S6: Based on the resistance impedance distribution image, determine the resistance impedance abnormal area inside the environment.

2. The resistance impedance detection probe control method according to claim 1, characterized in that: In step S1, specifically: Dynamically detect the liquid in the environment where the resistance impedance detection probe is located to obtain the variation characteristics of the size of the infiltration range of the liquid on the probe surface and the spatial variation characteristics of the flow speed of the liquid; In step S2, specifically: Based on the variation characteristics of the size of the infiltration range and the distribution range characteristics of the electrodes on the probe surface, estimating the range information of the effective excitation of the electrodes on the probe surface by the liquid in the environment; Based on the spatial variation characteristics of the flow velocity and the range information of the effective excitation of the electrode on the probe surface by the liquid, the spatial distribution information of the liquid ion flow on the probe surface in the environment is estimated; wherein the spatial distribution information of the liquid ion flow includes the size distribution information of the liquid ion flow migration rate at different positions of the probe surface in the environment.

3. The resistance impedance detection probe control method according to claim 1, characterized in that: In step S3, specifically: Based on the spatial distribution information of the liquid ion flow, the spatial distribution information of the bioelectric current intensity formed by the liquid ions on the probe surface is estimated; based on the spatial distribution information of the bioelectric current intensity and the detection coverage range corresponding to all the electrodes on the probe surface, the drift change characteristics of the bioelectric signal generated by all the electrodes are estimated; wherein the bioelectric signal drift change characteristics are the time domain change characteristics of the bioelectric signal intensity fluctuation formed by the liquid ion flow migration in the detection coverage range of the electrode; Based on the bioelectric signal drift change characteristics, the bioelectric signal intensity fluctuation change frequency and the bioelectric signal intensity fluctuation change difference corresponding to the detection coverage range of the electrode are obtained; based on the bioelectric signal intensity fluctuation change frequency and the bioelectric signal intensity fluctuation change difference, the electrical signal detection frequency and the electrical signal detection sensitivity of the electrode are adjusted respectively; In step S4, specifically: Perform frequency domain analysis on the bioelectric signal queues collected by all electrodes on the probe surface to obtain signal frequency size distribution information of the bioelectric signal queues collected by the electrodes; estimate the frequency domain range of the noise component of the bioelectric signal queue based on the signal frequency size distribution information; and adjust the signal noise reduction filter processing parameters of the signal processing end corresponding to the electrode based on the noise component frequency domain range.

4. The resistance impedance detection probe control method according to claim 1, characterized in that: In step S5, specifically: Acquire spatial posture change information of the probe in the environment, and determine position change information of all electrodes on the probe surface in the environment based on the spatial posture change information and the distribution position information of all electrodes on the probe surface; Based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface in the environment, a resistance impedance distribution sub-image of a corresponding subspace inside the environment obtained by the probe corresponding to each spatial posture detection when the probe is located in the environment with several different spatial postures is generated, and all resistance impedance distribution sub-images are integrated into a resistance impedance distribution image of the global scope inside the environment; In step S6, specifically: The resistance impedance distribution image is subjected to the recognition of the spatial variation of the impedance value, and the region with abnormal impedance variation rate in the global range within the environment is determined as the resistance impedance abnormal region within the environment.

5. A resistance impedance detection probe control device, characterized in that: The resistance impedance detection probe control device is used to implement the resistance impedance detection probe control method according to any one of claims 1 to 4, and the resistance impedance detection probe control device includes the following modules: An environment detection module, used to implement the above step S1; A liquid ion flow estimation module, used to implement the above step S2; An electrode electrical signal detection and adjustment module, used to implement the above step S3; A signal processing parameter adjustment module, used to implement the above step S4; A resistance impedance distribution identification module, used to implement the above step S5; The resistance impedance abnormal area positioning module is used to implement the above step S6.

6. A resistance impedance detection probe control system, characterized in that: The system comprises: The resistance impedance detection probe control device as claimed in claim 5; A visualization display device is used to generate a visualization image of the impedance change rate abnormal area in the global range inside the environment according to the impedance change rate abnormal area determined by the resistance impedance detection probe control device.

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