A method, device and system for controlling a resistance impedance detection probe

Abstract

The present invention relates to the field of impedance detection, and specifically to a method, device and system for controlling an impedance detection probe, which detect the liquid state characteristics of the environment where the impedance detection probe is located, thereby estimating the spatial distribution information of the liquid ion flow on the probe surface, and further estimating the drift change characteristics of the bioelectric signals formed by the liquid ions in the detection coverage area corresponding to the electrodes, and adjusting the electrical signal detection parameters of the electrodes; also based on the change characteristics of the bioelectric signal queues collected by all the electrodes on the probe surface, adjusting the signal processing parameters of the signal processing ends corresponding to the electrodes; based on the impedance information generated by the signal processing ends and the position change information of all the electrodes on the probe surface in the environment, generating an impedance distribution image, so as to determine the impedance abnormal area inside the environment. The present invention can adjust the working state of the probe during the change process of the liquid environment inside the human tissue, so as to accurately detect the bioelectric signals of the liquid environment.

Description

Technical Field

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

[0002] Resistance impedance exists in objects generally. For human tissues, the resistance impedance inside human tissues is related to tissue structure and type. When human tissues are in a healthy state, the corresponding resistance impedance and the resistance impedance of other surrounding tissues basically show a uniform or smooth change; when there are lesions such as tumors in human tissues, the corresponding resistance impedance and the resistance impedance of other non-lesioned tissues around will have a large difference. Therefore, by detecting the resistance impedance of human tissues, it can provide a reliable basis for identifying internal lesions of human tissues, and it 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 prior art uses a resistance impedance detection probe to penetrate into the spine, and uses multiple electrodes on the surface of the probe to detect the bioelectric signals in the internal body fluid environment of the spine, and analyzes the bioelectric signals to obtain the resistance impedance distribution in the internal body fluid environment of the spine. It is precisely because multiple electrodes are distributed on the surface of the probe that bioelectric signals in different regions of the internal body fluid environment of the spine can be obtained in one detection process. Bioelectric signals are formed by the combined action of ion flow in the body fluid and the resistance impedance of the biological tissues inside the spine. The greater the ion flow velocity or the greater the resistance impedance, the stronger the bioelectric signal. In actual detection, affected by factors such as the flow state of the internal body fluid of the spine and the infiltration state of the body fluid on the surface of the probe, some electrodes on the surface of the probe may not be able to form good contact with the body fluid or cannot accurately detect the change of the bioelectric signal in the body fluid environment in time, and cannot form an accurate and reliable detection of the entire global range inside the spine. Therefore, how to adjust the working state of the probe during the change of the internal liquid environment of human tissues and expect to accurately detect the bioelectric signal of the liquid environment is of great significance for improving the detection accuracy and reliability of the resistance impedance of the probe. Summary of the Invention

[0004] In order to avoid the electrodes on the surface of the probe from not being able to form good contact with the liquid or accurately detect the change of the bioelectric signal in the liquid environment in time, and thus unable to ensure the detection accuracy and reliability of the resistance impedance of the probe, the present invention provides a method for controlling a resistance impedance detection probe, and the method includes the following steps:

[0005] S1: Detect the environment where the resistance impedance detection probe is located to obtain the liquid state characteristics of the environment;

[0006] S2: Estimate the spatial distribution information of liquid ion flow on the surface of the probe based on the liquid state characteristics;

[0007] S3: Estimate the characteristics of the drift change of the bioelectric signal formed by the detection coverage areas corresponding to each electrode on the surface of the probe based on the spatial distribution information of the liquid ion flow; adjust the signal detection parameters of each electrode on the surface of the probe based on the characteristics of the drift change of the bioelectric signal.

[0008] S4: Adjust the signal processing parameters of the signal processing ends corresponding to each electrode based on the change characteristics of the bioelectric signal queues collected by each electrode on the surface of the probe.

[0009] S5: Generate the 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 surface of the probe in the environment.

[0010] S6: Determine the resistance impedance abnormal areas inside the environment based on the resistance impedance distribution image.

[0011] Preferably, in step S1, specifically:

[0012] Dynamically detect the liquid in the environment where the resistance impedance detection probe is located to obtain the change characteristics of the wetting range size of the liquid on the surface of the probe and the spatial change characteristics of the flow velocity of the liquid.

[0013] In step S2, specifically:

[0014] Estimate the range information of the effective excitation of the electrodes on the surface of the probe by the liquid in the environment based on the change characteristics of the wetting range size and the electrode distribution range characteristics on the surface of the probe.

[0015] Estimate the spatial distribution information of the liquid ion flow on the surface of the probe in the environment based on the spatial change characteristics of the flow velocity and the range information of the effective excitation of the electrodes on the surface of the probe by the liquid; wherein, the spatial distribution information of the liquid ion flow includes the distribution information of the magnitudes of the liquid ion flow migration rates at different positions on the surface of the probe in the environment.

[0016] Preferably, in step S3, specifically:

[0017] Estimate the spatial distribution information of the bioelectric current intensity formed by the liquid ions on the surface of the probe based on the spatial distribution information of the liquid ion flow; estimate the characteristics of the drift change of the bioelectric signals generated by each electrode based on the spatial distribution information of the bioelectric current intensity and the detection coverage areas corresponding to each electrode on the surface of the probe; wherein, the characteristics of the drift change of the bioelectric signal are the time-domain change characteristics of the bioelectric signal intensity fluctuation formed by the liquid ion flow migration in the detection coverage area of the electrode.

[0018] Based on the drift change characteristics of the bioelectrical signals, obtain the frequency of the fluctuation change of the bioelectrical signal intensity and the difference of the fluctuation change of the bioelectrical signal intensity corresponding to the detection coverage range of the electrode; based on the frequency of the fluctuation change of the bioelectrical signal intensity and the difference of the fluctuation change of the bioelectrical signal intensity, adjust the electrical signal detection frequency and the electrical signal detection sensitivity of the electrode respectively;

[0019] In step S4, specifically:

[0020] Perform frequency-domain analysis on the bioelectrical signal queues collected by all the electrodes on the probe surface respectively to obtain the signal frequency magnitude distribution information of the bioelectrical signal queues collected by the electrodes; based on the signal frequency magnitude distribution information, estimate the frequency-domain range of the noise components of the bioelectrical signal queues; based on the frequency-domain range of the noise components, adjust the signal noise reduction and filtering processing parameters of the signal processing end corresponding to the electrodes.

[0021] Preferably, in step S5, specifically:

[0022] Obtain the spatial attitude change information of the probe in the environment, and based on the spatial attitude change information and the distribution position information of all the electrodes on the probe surface, determine the position change information of all the electrodes on the probe surface in the environment;

[0023] Based on the resistance impedance information generated by the signal processing end and the position change information of all the electrodes on the probe surface in the environment, generate resistance impedance distribution sub-images of the corresponding sub-spaces inside the environment detected by the probe when the probe is located in the environment in several different spatial attitudes, and integrate all the resistance impedance distribution sub-images into a resistance impedance distribution image of the global range inside the environment;

[0024] In the said step S6, specifically:

[0025] Perform identification of the spatial change of the impedance value magnitude on the resistance impedance distribution image to determine the impedance change rate abnormal area of the global range inside the environment, and use this as the resistance impedance abnormal area inside the environment.

[0026] On the other hand, the present invention provides a resistance impedance detection probe control device, and the above resistance impedance detection probe control device is used to implement the resistance impedance detection probe control method as described above. The resistance impedance detection probe control device includes the following modules:

[0027] An environment detection module, which is used to implement the above step S1;

[0028] A liquid ion flow estimation module, which is used to implement the above step S2;

[0029] The electrode electrical signal detection and adjustment module is used to implement the above step S3;

[0030] The signal processing parameter adjustment module is used to implement the above step S4;

[0031] The resistance impedance distribution identification module is used to implement the above step S5;

[0032] The resistance impedance abnormal area positioning module is used to implement the above step S6.

[0033] In addition, the present invention also provides a resistance impedance detection probe control system, and the system includes:

[0034] The above-mentioned resistance impedance detection probe control device;

[0035] The 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.

[0036] Compared with the prior art, the present invention has the following beneficial effects:

[0037] Detect the environment where the resistance impedance detection probe is located to obtain the liquid state characteristics of the environment; based on the liquid state characteristics, estimate the spatial distribution information of the liquid ion flow on the probe surface. 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 infiltrated into the body fluid environment, the probe will not be able to comprehensively collect the bioelectric signals inside the body fluid environment. Moreover, there are differences in the ion flow migration states in different regions of the body fluid environment, and the detection sensitivity of the electrodes on the probe surface directly affects the reliability of the electrodes to collect bioelectric signals. In order to ensure that the electrodes on the probe surface can adapt to the ion flow migration states in different regions inside the body fluid environment for accurate and efficient detection and collection, it is necessary to pre-detect the liquid state characteristics of the environment where the probe is located, so as to estimate the spatial distribution information of the liquid flow in the environment at different positions on the probe surface, so that the electrodes at different positions on the probe surface can collect bioelectric signals in a matching mode, and maximize the credibility of the bioelectric signal collection of all electrodes on the probe surface.

[0038] Estimate the drift change characteristics of bioelectrical signals formed by the detection coverage areas corresponding to each electrode on the probe surface based on the spatial distribution information of liquid ion flow; adjust the electrical signal detection parameters of each electrode on the probe surface based on the drift change characteristics of bioelectrical signals. After the probe is immersed in the body fluid environment inside the human body, the liquid ion flow conditions in the body fluid environment areas directly contacted by the electrodes at different positions on the probe surface are not the same. If all the electrodes on the probe surface collect bioelectrical signals in the same mode, it will not be possible to ensure that the collected bioelectrical signals truly reflect the magnitude of the bioelectrical signals in the body fluid environment area directly contacted by themselves. In addition, each electrode on the probe surface corresponds to a specific detection coverage area, resulting in different bioelectrical signal intensity change conditions formed in the detection coverage area corresponding to each electrode due to liquid ion flow. The bioelectrical signal intensity fluctuates relatively fast in the detection coverage area corresponding to some electrodes, relatively slowly in the detection coverage area corresponding to some other electrodes, with a relatively large difference in the fluctuation change of the bioelectrical signal intensity in the detection coverage area corresponding to some other electrodes, and a relatively small difference in the fluctuation change of the bioelectrical signal pressure in the detection coverage area corresponding to some other electrodes. If all the electrodes on the probe surface collect the bioelectrical signals in their corresponding detection coverage areas with the same detection frequency and detection sensitivity, problems such as missing or incorrect detection of bioelectrical signals may occur. Therefore, based on the spatial distribution information of liquid ion flow in the body fluid environment, estimate the drift change characteristics of bioelectrical signals formed by liquid ion flow migration in the detection coverage areas corresponding to each electrode on the probe surface, and adjust the electrical signal detection parameters of each electrode on the probe surface to ensure that each electrode can collect bioelectrical signals in a matching electrical signal detection mode, improving the detection accuracy of bioelectrical signals.

[0039] Adjust the signal processing parameters of the signal processing ends corresponding to each electrode based on the change characteristics of the bioelectrical signal queues collected by each electrode on the probe surface. All the electrodes on the probe surface are connected to signal processing ends for processing the bioelectrical signals collected by each electrode to obtain resistance impedance information. Given that the signal-to-noise ratios of the bioelectrical signals collected by different electrodes in their respective detection coverage areas are not the same, the noise reduction filtering processing modes required before converting the bioelectrical signals into resistance impedance information are also correspondingly different. In order to accurately perform noise reduction filtering processing on the bioelectrical signals collected by each electrode on the probe surface, first identify the frequency magnitude distribution of the bioelectrical signal queues collected by each electrode in the corresponding time period to obtain the frequency magnitude conditions of all the signal components subordinate to the bioelectrical signal queues, thereby estimating the frequency domain range of the noise components of the bioelectrical signal queues, and then specifically adjust the signal noise reduction filtering processing parameters of the corresponding signal processing ends to ensure that the bioelectrical signals generated by each electrode can be effectively subjected to noise reduction filtering, improving the accuracy of converting the bioelectrical signals into resistance impedance information subsequently.

[0040] 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 ensure the collection of bioelectric signals in the global range of the body fluid environment inside human tissues. Therefore, in actual detection operations, it is necessary to change the spatial attitude angle of the probe in the body fluid environment after it is inserted into human tissues in order to collect bioelectric signals from different regions in the body fluid environment. Whenever the probe switches to a spatial attitude 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 different spatial attitude angles of the probe are integrated into a resistance impedance distribution image of the global range in the body fluid environment, so as to accurately and comprehensively characterize the size distribution of the resistance impedance of the whole human tissue. As previously introduced, when there are lesions such as tumors in human tissues, there are significant differences in the resistance impedance between the lesion area and the non-lesion area. By identifying the spatial change of impedance values in the resistance impedance distribution image, the abnormal area of impedance change in the global range of the body fluid environment of human tissues is determined, providing a reliable basis for identifying the internal lesions of human tissues. BRIEF DESCRIPTION OF THE DRAWINGS

[0041] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the following will briefly introduce the drawings required for the description of the embodiments. Obviously, the following drawings are only some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings. Among them:

[0042] Figure 1 is a flowchart of a method for controlling a resistance impedance detection probe provided by the present invention.

[0043] Figure 2 is a structural diagram of a device for controlling a resistance impedance detection probe provided by the present invention.

[0044] Figure 3 is a structural diagram of a system for controlling a resistance impedance detection probe provided by the present invention. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0045] To make the above objects, features, and advantages of the present invention more obvious and understandable, the following will describe in detail the specific embodiments of the present invention with reference to the accompanying drawings. It can be understood that the specific embodiments described herein are only for explaining the present invention and not for limiting the present invention. Additionally, it should be noted that for the sake of convenience of description, only the parts related to the present invention rather than all the structures are shown in the drawings. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts fall within the scope of protection of the present invention.

[0046] The terms "comprise" and "have" in the present invention and any variations thereof are intended to cover non-exclusive inclusion. For example, a process, method, system, product, or device that includes a series of steps or units is not limited to the listed steps or units, but optionally further includes steps or units not listed, or optionally further includes other steps or units inherent to these processes, methods, products, or devices.

[0047] Referring to "embodiments" herein means that the specific features, structures, or characteristics described in connection with the embodiments can be included in at least one embodiment of the present invention. The phrase appearing at various positions in the specification does not necessarily refer to the same embodiment, nor is it an independent or alternative embodiment mutually exclusive with other embodiments. Those skilled in the art explicitly and implicitly understand that the embodiments described herein can be combined with other embodiments.

[0048] Please refer to Figure 1 As shown, the present invention provides a method for controlling a resistance impedance detection probe, and the method includes the following steps:

[0049] S1: Detect the environment where the resistance impedance detection probe is located to obtain the liquid state characteristics of the environment;

[0050] S2: Based on the liquid state characteristics, estimate the spatial distribution information of the liquid ion flow on the probe surface.

[0051] Further, in step S1, specifically:

[0052] Dynamically detect the liquid in the environment where the resistance impedance detection probe is located to obtain the change characteristics of the wetting range size of the liquid on the probe surface and the spatial change characteristics of the liquid flow velocity.

[0053] Further, in step S2, specifically:

[0054] Based on the change characteristics of the wetting range size and the electrode distribution range characteristics on the probe surface, estimate the range information of the effective excitation of the electrodes on the probe surface by the liquid in the environment;

[0055] Estimate the spatial distribution information of liquid ion flow on the probe surface in the environment 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; wherein, the spatial distribution information of liquid ion flow includes the magnitude distribution information of the liquid ion flow migration rate at different positions of the probe surface in the environment.

[0056] Human tissues such as the spine contain fluid that can flow. During the flow of the body fluid, the ions inside the body fluid will also flow accordingly, thus forming bioelectric signals (such as bio-voltage signals or bio-current signals). The intensity of the bioelectric signal is associated with the resistance impedance of the human tissue. By detecting and collecting the bioelectric signals in the body fluid environment inside the human tissue, the resistance impedance distribution of the body fluid environment inside the human tissue can be calculated and determined. This does not require an additional excitation voltage or excitation current to be applied to the body fluid environment inside the human tissue. 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 uniformly distributed on the surface of the probe carrier; wherein, the probe carrier can have an elongated external shape structure to facilitate 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 high cloud semiconductor GW1NR-9 FPGA chip.

[0057] When a probe is inserted into human tissues such as the spine, the probe will be immersed in the body fluid environment inside the human tissues. The ion flow and migration state in the body fluid environment directly affect the detection state and results of the bioelectric signals of the surface electrodes of the probe on the body fluid environment. If some of the surface electrodes of the probe are not immersed in the body fluid environment, the probe will not be able to comprehensively collect the bioelectric signals inside the body fluid environment. In addition, there are differences in the ion flow and migration states in different regions of the body fluid environment, and the detection sensitivity of the surface electrodes of the probe 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 and migration speed in the body fluid environment directly affect the bioelectric signal collection state of the electrodes. 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, a plurality of pressure sensors and a plurality of flow sensors can be uniformly arranged on the surface of the probe carrier, and all the pressure sensors and the flow sensors are regularly arranged alternately with all the electrodes. After the probe is immersed in the body fluid environment and subjected to the action of body fluid pressure, the pressure on the area of the probe surface immersed in the body fluid will increase significantly. By analyzing the pressure data collected by each of all the pressure sensors, the range of the probe surface immersed in the body fluid can be judged, and the electrodes located in the range of the probe surface immersed in the body fluid will be correspondingly affected by the ions inside the body fluid and detect bioelectric signals. The greater the body fluid flow speed in the body fluid environment, the greater the ion flow speed in the body fluid, and the stronger the corresponding bioelectric signal. However, the body fluid flow speed in the body fluid environment is not uniform, and there are differences in the body fluid flow speeds in different regions of the body fluid environment. In order to enable the electrodes to detect the bioelectric signals formed in the body fluid environment area where they are 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 distribution information of the body fluid ion flow and migration magnitudes at different positions on the probe surface in the body fluid environment, so as to provide a reliable basis for adjusting the bioelectric signal detection parameters of different electrodes on the probe surface in the future.

[0058] Specifically, the body fluid in the body fluid environment where the probe is located is dynamically detected through the pressure sensor and the flow rate sensor on the probe surface, and the pressure distribution data exerted by the body fluid on the probe surface and the flow rate distribution data of the body fluid on the probe surface are obtained; then the pressure distribution data and the flow rate distribution data are analyzed to obtain the change characteristics of the wetted area size of the body fluid on the probe surface and the spatial change characteristics of the flow velocity. Then, in combination with the change characteristics of the wetted area size on the probe surface and the electrode distribution range characteristics 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 change characteristics of the wetted area size on the probe surface and the electrode distribution range characteristics on the probe surface, the proportion of the surface area wetted by the body fluid for each electrode is determined. If the surface area proportion exceeds a preset proportion threshold, it is determined that the electrode can be effectively excited by the body fluid, and the surface range occupied by all the electrodes effectively excited by the body fluid on the probe surface is determined as the effective excitation range on the probe surface. From the above analysis, it can be seen that the flow of the body fluid drives the flow of ions inside it to form a bioelectric signal, and there are differences in the flow velocity of the body fluid in different regions of the body fluid environment, providing a basis for accurately adjusting the method of detecting the bioelectric signal by the electrodes subsequently. Therefore, based on the spatial change 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 liquid ion flow migration rate at different positions of the probe surface in the body fluid environment is estimated.

[0059] 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 corresponding to each electrode on the probe surface; based on the drift change characteristics of the bioelectric signal, adjust the signal detection parameters of each electrode on the probe surface;

[0060] S4: Based on the change characteristics of the bioelectric signal queue collected by each electrode on the probe surface, adjust the signal processing parameters of the signal processing ends corresponding to each electrode.

[0061] Further, in step S3, specifically:

[0062] Based on the spatial distribution information of the liquid ion flow, estimate the spatial distribution information of the bioelectric current intensity formed by the liquid ions on the probe surface; based on the spatial distribution information of the bioelectric current intensity and the detection coverage corresponding to each electrode on the probe surface, estimate the drift change characteristics of the bioelectric signals generated by each electrode; among them, the drift change characteristics of the bioelectric signal are the time-domain change characteristics of the bioelectric signal intensity fluctuation formed by the liquid ion flow migration in the detection coverage of the electrode.

[0063] Based on the drift change characteristics of bioelectrical signals, obtain the frequency of the fluctuation change of the bioelectrical signal intensity and the difference value of the fluctuation change of the bioelectrical signal intensity corresponding to the detection coverage range of the electrode; based on the frequency of the fluctuation change of the bioelectrical signal intensity and the difference value of the fluctuation change of the bioelectrical signal intensity, respectively adjust the electrical signal detection frequency and the electrical signal detection sensitivity of the electrode.

[0064] After the probe is immersed in the body fluid environment inside the human body, the liquid ion flow conditions in the body fluid environment areas directly contacted by the electrodes at different positions on the probe surface are not the same. If all the electrodes on the probe surface adopt the same mode to collect bioelectrical signals, it will not be possible to ensure that the collected bioelectrical signals truly reflect the size of the bioelectrical signals in the body fluid environment area directly contacted by themselves. In addition, each of the electrodes on the probe surface corresponds to a specific detection coverage range, resulting in different bioelectrical signal intensity change conditions formed in the detection coverage range corresponding to each electrode due to liquid ion flow. The bioelectrical signal intensity fluctuation changes relatively fast in the detection coverage range corresponding to a part of the electrodes, and relatively slow in the detection coverage range corresponding to another part of the electrodes. There is also a relatively large difference value in the fluctuation change of the bioelectrical signal intensity in the detection coverage range corresponding to a part of the electrodes, and a relatively small difference value in the pressure fluctuation change of the bioelectrical signal in the detection coverage range corresponding to another part of the electrodes. If all the electrodes on the probe surface adopt the same detection frequency and detection sensitivity to collect the bioelectrical signals in their corresponding detection coverage ranges, it may lead to problems such as missing or incorrect detection of bioelectrical signals.

[0065] Therefore, based on the spatial distribution information of the liquid ion flow in the body fluid environment, estimate the drift change characteristics of the bioelectrical signals formed in the detection coverage range corresponding to each of the electrodes on the probe surface due to the liquid ion flow migration, and adjust the electrical signal detection parameters of each of the electrodes on the probe surface to ensure that each electrode can collect bioelectrical signals in a matching electrical signal detection mode, thereby improving the detection accuracy of bioelectrical signals. Specifically, based on the frequency of the fluctuation change of the bioelectrical signal intensity, determine whether the frequency of the fluctuation change of the bioelectrical 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, increase the electrical signal detection frequency of the electrode; if not, keep the electrical signal detection frequency of the electrode unchanged. Based on the drift change characteristics of the bioelectrical signals, determine whether the difference value of the fluctuation change of the bioelectrical signal intensity corresponding to the detection coverage range of the electrode is less than the electrical signal detection sensitivity of the electrode; if so, increase the electrical signal detection sensitivity of the electrode; if not, keep the electrical signal detection sensitivity of the electrode unchanged. Through the above method, it can be ensured that the electrodes on the probe surface collect the bioelectrical signals in their corresponding detection coverage ranges in the body fluid environment with appropriate electrical signal detection frequencies and electrical signal detection sensitivities.

[0066] Furthermore, in step S4, specifically:

[0067] Perform frequency domain analysis on the bioelectrical signal queues collected by each electrode on the probe surface to obtain the signal frequency magnitude distribution information of the bioelectrical signal queues collected by the electrodes; based on the signal frequency magnitude distribution information, estimate the frequency domain range of the noise components of the bioelectrical signal queues; based on the frequency domain range of the noise components, adjust the signal noise reduction filtering processing parameters of the signal processing end corresponding to the electrodes.

[0068] Given that the signal-to-noise ratios of the bioelectrical signals collected by different electrodes within their respective detection coverage ranges are not the same, the noise reduction filtering processing modes required before converting the bioelectrical signals into resistance impedance information are also correspondingly different. To accurately perform noise reduction filtering processing on the bioelectrical signals collected by each electrode on the probe surface, first perform signal frequency magnitude distribution identification on the bioelectrical signal queues collected by each electrode during the corresponding time period to obtain the frequency magnitudes of all signal components subordinate to the bioelectrical signal queues, thereby estimating the frequency domain range of the noise components of the bioelectrical signal queues, and then adjust the signal noise reduction filtering processing parameters of the corresponding signal processing end accordingly, such as the frequency threshold range of the signal noise reduction filtering processing, to ensure that the bioelectrical signals generated by each electrode can be effectively subjected to noise reduction filtering, improving the accuracy of subsequent conversion of bioelectrical signals into resistance impedance information.

[0069] S5: Generate 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 within the environment;

[0070] S6: Determine the resistance impedance abnormal area inside the environment based on the resistance impedance distribution image.

[0071] Furthermore, in step S5, specifically:

[0072] Obtain the spatial attitude change information of the probe within the environment, and based on the spatial attitude change information and the distribution position information of all electrodes on the probe surface, determine the position change information of all electrodes on the probe surface within the environment;

[0073] Based on the resistance impedance information generated by the signal processing end and the position change information of all electrodes on the probe surface within the environment, generate sub-images of the resistance impedance distribution of the corresponding sub-spaces inside the environment detected by the probe for each spatial attitude when the probe is located within the environment in several different spatial attitudes, and integrate all the sub-images of the resistance impedance distribution into a resistance impedance distribution image of the global range inside the environment.

[0074] Furthermore, in step S6, specifically:

[0075] Perform identification of the spatial change of the impedance value magnitude on the resistance impedance distribution image to determine the area with abnormal impedance change rate in the global range inside the environment, and use this as the resistance impedance abnormal area inside the environment.

[0076] Limited by the small size of the probe itself, setting multiple electrodes on the probe surface cannot guarantee the acquisition of bioelectrical signals in the global range of the body fluid environment inside human tissues. Therefore, in actual detection operations, it is necessary to change the spatial attitude angle of the probe in the body fluid environment after it is inserted into human tissues in order to collect bioelectrical signals from different regions in the body fluid environment. Whenever the probe switches to a spatial attitude angle in the body fluid environment, the bioelectrical signals collected by all the electrodes on the probe surface are collected, and combined with the position information of all the electrodes on the probe surface in the body fluid environment, a sub-image of the resistance impedance distribution of the corresponding subspace inside the body fluid environment is generated. Then, the sub-images of the resistance impedance distribution corresponding to different spatial attitude angles of the probe are integrated into a resistance impedance distribution image of the global range in the body fluid environment, so as to accurately and comprehensively characterize the distribution of the resistance impedance magnitude of the whole human tissue. As previously introduced, when there are lesions such as tumors in human tissues, there are significant differences in the resistance impedance between the lesion area and the non-lesion area. By identifying the spatial variation of the impedance value in the resistance impedance distribution image, the abnormal impedance change area in the global range of the body fluid environment of human tissues is determined, thus providing a reliable basis for identifying the internal lesion conditions of human tissues.

[0077] Please refer to Figure 2 As shown, the present invention provides a control device for a resistance impedance detection probe, which is used to implement the above-mentioned resistance impedance detection probe control method. The device includes the following modules:

[0078] An environment detection module, which is used to implement the above step S1;

[0079] A liquid ion flow estimation module, which is used to implement the above step S2;

[0080] An electrode electrical signal detection and adjustment module, which is used to implement the above step S3;

[0081] A signal processing parameter adjustment module, which is used to implement the above step S4;

[0082] A resistance impedance distribution recognition module, which is used to implement the above step S5;

[0083] A resistance impedance abnormal area positioning module, which is used to implement the above step S6.

[0084] The operation and effect of the resistance impedance detection probe control device of the present invention are corresponding and consistent with the above-mentioned resistance impedance detection probe control method, and the description of the resistance impedance detection probe control device will not be repeated here.

[0085] Please refer to Figure 3 As shown, the present invention provides a resistance impedance detection probe control system, which includes:

[0086] The above-mentioned resistance impedance detection probe control device;

[0087] A visualization display device, which 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.

[0088] In the above-mentioned resistance impedance detection probe control system, the visualization display device can be, but is not limited to, a flat display device or a three-dimensional display device, etc. In this way, the visualization display device can generate a visualization image of the impedance change rate abnormal area in the global range inside the body fluid environment of the human tissue according to the impedance change rate abnormal area from the resistance impedance detection probe control device, so as to preliminarily locate the area where lesions may occur inside the human tissue and provide a reliable basis for subsequent diagnosis and treatment.

[0089] Through the description of the above embodiments, those skilled in the art can clearly understand that each embodiment can be implemented by means of adding a necessary general hardware platform, and of course, it can also be implemented by a combination of hardware and software. Based on such an understanding, the above technical solution, in essence, or the part that contributes to the prior art can be embodied in the form of a computer product. The present invention can adopt the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk memories, CD-ROMs, optical memories, etc.) containing computer-usable program codes.

[0090] Finally, it should be noted that: the above embodiments are only used to illustrate the technical solutions of the present invention, rather than limiting it, and other embodiments can also be adopted; although the present invention has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that: they can still modify the technical solutions recorded in the foregoing embodiments, or perform equivalent replacements on some of the technical features; and these modifications or replacements do not make the essence of the corresponding technical solutions 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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