An interfering electrical device for assisting in the treatment of arthritis

Abstract

The present application relates to the field of ultrasonic therapy technology, and provides an interfering electrical device for assisting in the treatment of arthritis. The device utilizes ultrasound through an ultrasonic detection unit to comprehensively detect the target joint part, and accurately identifies the boundary of the joint cavity during the detection process. At the same time, the detection layer is determined and scanned based on the depth of the target joint part to obtain the ultrasonic attenuation coefficient of different detection layers, which can provide a more comprehensive and detailed understanding of the conditions of each layer of tissue inside the joint; the intelligent adjustment unit can accurately determine the location, area and degree of inflammation based on the ultrasonic attenuation coefficient obtained by the ultrasonic detection unit, and generate interfering electrical parameters based on the determined inflammation information. According to the interfering electrical parameters and the electrode combination layout, the interfering electrical directional output acts on the inflammatory position of the target joint part, which greatly improves the accuracy of the treatment, reduces the adverse effects on normal tissues, and improves the treatment effect and the comfort of the patient.

Description

Technical Field

[0001] The present application relates to the technical field of ultrasonic therapy, and in particular to an interfering electrical device for assisting in the treatment of arthritis. Background Art

[0002] There are some limitations in the existing interferential electrical devices used to assist in the treatment of arthritis. For example, in terms of detection, traditional detection methods cannot accurately obtain the boundaries and morphology of inflammation inside the joint. In addition, most detection methods do not consider the impact of differences in joint depth on the test results, and cannot perform stratified detection and obtain the ultrasonic attenuation coefficients of tissues at different depths, making it difficult to fully reflect the true condition inside the joint.

[0003] From a treatment perspective, existing interferential electrical devices lack specificity and personalization. Interferential electrical parameters often use fixed settings or simple manual adjustment methods, and cannot be intelligently adjusted according to the patient's specific inflammatory conditions. Moreover, when interfering electricity is output, it is difficult to achieve precise directional focusing, which often causes unnecessary stimulation to surrounding normal tissues, which not only affects the treatment effect but may also cause discomfort to the patient. Summary of the Invention

[0004] In view of the shortcomings of the existing technology, the present application provides an interfering electrical device for assisting in the treatment of arthritis, the device comprising: a detection and adjustment module, the detection and adjustment module comprising an ultrasonic detection unit and an intelligent adjustment unit;

[0005] The ultrasonic detection unit is used to detect the target joint part through ultrasound, identify the boundary of the joint cavity and segment the synovium and articular cartilage, determine the detection layer based on the depth of the target joint part and scan it, obtain the ultrasonic attenuation coefficient of different detection layers, and generate the joint ultrasonic attenuation distribution map after fusion;

[0006] The intelligent adjustment unit is used to determine the location, area and degree of inflammation based on the joint ultrasonic attenuation distribution map, generate interference electrical parameters, and arrange the interference electrical combination according to the interference electrical parameters so that the interference electrical directional output acts on the inflammation location of the target joint.

[0007] As an optional implementation, the detection logic of the target joint part includes:

[0008] Select the target joint area, apply ultrasound to cover the target joint area in a sector scanning mode, and generate an initial ultrasound grayscale image based on the ultrasound echo intensity;

[0009] The joint cavity boundary is identified based on the initial ultrasound grayscale image, and the synovium and articular cartilage are segmented through image registration algorithm to determine the target detection area;

[0010] Determine the detection layer according to the depth of the target joint, adjust the ultrasound transmission frequency based on the detection layer, and scan the target detection area of ​​each detection layer through a spiral progressive scanning path to obtain the ultrasound attenuation coefficient of each detection layer;

[0011] The ultrasound attenuation coefficients of multiple detection layers are fused in real time to generate a joint ultrasound attenuation distribution map and mark abnormal attenuation areas.

[0012] As an optional implementation manner, the target detection area determination sub-logic includes:

[0013] Preprocessing and edge detection are performed on the initial ultrasonic grayscale image to identify the edge points of the joint cavity boundary, and curve fitting is performed on the edge points to obtain the joint cavity boundary;

[0014] The ultrasound grayscale image is registered with the standard joint image through a feature-based image registration algorithm, and the synovium and articular cartilage are segmented from the ultrasound grayscale image.

[0015] The target detection area is determined based on the recognition results of the joint cavity boundary and the segmentation results of the synovium and articular cartilage.

[0016] As an optional implementation manner, the logic for obtaining the ultrasonic attenuation coefficient includes:

[0017] Record the ultrasound emission frequency and emission intensity, and record the echo intensity of different detection layers;

[0018] Perform distance correction on the echo intensities of different detection layers to obtain the corrected echo intensities;

[0019] The ultrasonic attenuation coefficients of different detection layers are calculated based on the ultrasonic emission intensity, the corrected echo intensity, and the propagation distances of different detection layers.

[0020] As an optional embodiment, the logic for determining the inflammation location, inflammation area, and inflammation degree includes:

[0021] Receive the joint ultrasound attenuation distribution map and preliminarily screen out abnormal attenuation areas through threshold segmentation;

[0022] Based on morphological operations, adjacent abnormal attenuation areas are connected to form the outline of the inflammation area;

[0023] The center coordinates of the inflammation area were calculated using the centroid algorithm and marked as the inflammation location;

[0024] Count the total number of pixels in the inflammation area to obtain the inflammation area;

[0025] The degree of inflammation was determined based on the mean value of the ultrasound attenuation coefficient within the inflamed area.

[0026] As an optional implementation manner, the generation logic of the interference electrical parameter includes:

[0027] Interference electrical parameters include the amplitude, frequency and waveform of interference electricity. The amplitude of interference electricity is generated according to the degree of inflammation and the area of ​​inflammation.

[0028] Determine the detection layer where the inflammation area is located to dynamically adjust the frequency of the interference electricity and determine the waveform of the interference electricity;

[0029] The ultrasonic attenuation coefficient is updated after the interfering electrical parameters act on the inflammation position, and the amplitude of the interfering electrical current is adjusted according to the decreasing rate of the ultrasonic attenuation coefficient.

[0030] As an optional implementation manner, the sub-logic for adjusting the amplitude of the interference voltage includes:

[0031] The amplitude of the interference current is calculated and adjusted according to the decrease rate of the ultrasonic attenuation coefficient;

[0032] applying the adjusted amplitude of the interfering electricity to the interfering electricity to direct the output toward the inflammation site;

[0033] The rate of decrease of the ultrasonic attenuation coefficient and the amplitude of the interference electricity are continuously monitored to trigger early warning processing.

[0034] As an optional implementation manner, the logic of interfering with electrical directional output includes:

[0035] Determine the electrode combination layout according to the location of inflammation, and monitor the tissue impedance when the electrodes are in contact with the skin in real time;

[0036] According to the generated interference electrical parameters and the electrode combination layout, the phase difference between the electrode combinations is calculated;

[0037] According to the phase difference between the electrode combinations, the interference electricity forms an electric field distribution in space, focusing on the inflammation site for directional output;

[0038] During the process of interfering electrical directional output, the change data of tissue impedance and ultrasonic attenuation coefficient are monitored in real time to determine whether to dynamically adjust the phase difference between the electrode combinations and the interfering electrical parameters.

[0039] As an optional implementation manner, the sub-logic for adjusting the phase difference between electrode combinations includes:

[0040] Determine the phase delay caused by tissue impedance and determine the phase compensation value;

[0041] The phase difference between the electrode combinations is recalculated based on the phase compensation value.

[0042] Compared with the existing technology, the beneficial effects of the present application are: using ultrasound through the ultrasonic detection unit to comprehensively detect the target joint part, and accurately identifying the boundary of the joint cavity during the detection process, while determining the detection layer based on the depth of the target joint part and scanning to obtain the ultrasonic attenuation coefficient of different detection layers, which can more comprehensively and meticulously understand the conditions of each layer of tissue inside the joint, and generate a joint ultrasonic attenuation distribution map by fusing the ultrasonic attenuation coefficients of these different detection layers, which can clearly display the ultrasonic attenuation situation inside the joint, and provide rich and accurate data for subsequent analysis of inflammation.

[0043] Through the intelligent adjustment unit, based on the ultrasonic attenuation coefficient obtained by the ultrasonic detection unit, the location, area and degree of inflammation can be accurately determined, and interference electrical parameters can be generated according to the determined inflammation information, thereby realizing personalized customization of interference electrical treatment; and according to the interference electrical parameters and the electrode combination layout, the interference electrical directional output acts on the inflammation location of the target joint, which greatly improves the accuracy of the treatment, reduces the adverse effects on normal tissues, and enhances the treatment effect and patient comfort. BRIEF DESCRIPTION OF THE DRAWINGS

[0044] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following briefly introduces the drawings required for describing the embodiments. Obviously, the drawings described below are only some embodiments of the present application. For those skilled in the art, other drawings can be derived from these drawings without inventive work. Among them:

[0045] Figure 1 A device module diagram of an interfering electrical device for assisting in the treatment of arthritis provided in an embodiment of the present application;

[0046] Figure 2 A diagram showing the structure of an execution interaction device for an interfering electrical device for assisting in the treatment of arthritis provided in an embodiment of the present application;

[0047] Figure 3 A target joint detection logic diagram of an interfering electrical device for assisting in the treatment of arthritis provided in an embodiment of the present application;

[0048] Figure 4 This is a logic diagram for generating interference electrical parameters of an interference electrical device for assisting in the treatment of arthritis provided in an embodiment of the present application.

[0049] Figure numerals: 1. LCD touch panel; 2. Device handle; 3. Output intensity adjustment button; 4. Device status indicator light; 5. Adsorption electrode output port; 6. Self-adhesive electrode output port; 7. Slanted drawer; 8. Device body. DETAILED DESCRIPTION

[0050] In order to make the objectives, technical solutions and advantages of the embodiments of the present application more obvious and easy to understand, the technical solutions in the embodiments of the present application are clearly and completely described below in conjunction with the drawings in the specification. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments.

[0051] Example

[0052] like Figure 1 As shown, an embodiment of the present application provides a device module diagram of an interfering electrical device for assisting in the treatment of arthritis, wherein the device includes an execution interaction device and a detection and adjustment module.

[0053] like Figure 2 As shown, the interactive device includes a liquid crystal touch panel 1, a device handle 2, an output intensity adjustment button 3, a device status indicator light 4, an adsorption electrode output port 5, a self-adhesive electrode output port 6, a tilting drawer 7 and a device body 8.

[0054] The detection and adjustment module is integrated into the device body 8, and includes an ultrasonic detection unit and an intelligent adjustment unit.

[0055] The ultrasonic detection unit is used to detect the target joint part through ultrasound, identify the boundary of the joint cavity and segment the synovium and articular cartilage, determine the detection layer based on the depth of the target joint part and scan, obtain the ultrasonic attenuation coefficient of different detection layers, and generate the joint ultrasonic attenuation distribution map after fusion.

[0056] Specifically, if Figure 3 As shown in the figure, the detection logic of the target joint includes:

[0057] Select the target joint area, apply ultrasound to cover the target joint area in a sector scanning mode, and generate an initial ultrasound grayscale image based on the ultrasound echo intensity;

[0058] The joint cavity boundary is identified based on the initial ultrasound grayscale image, and the synovium and articular cartilage are segmented through image registration algorithm to determine the target detection area;

[0059] Determine the detection layer according to the depth of the target joint, adjust the ultrasound transmission frequency based on the detection layer, and scan the target detection area of ​​each detection layer through a spiral progressive scanning path to obtain the ultrasound attenuation coefficient of each detection layer;

[0060] The ultrasound attenuation coefficients of multiple detection layers are fused in real time to generate a joint ultrasound attenuation distribution map and mark abnormal attenuation areas.

[0061] Accurately detecting the target joint part is the basis for obtaining effective ultrasonic data and then judging the joint inflammation situation. The structures and positions of different joints are different, and targeted detection operations are required; the user selects the target joint part to be detected, such as the knee joint and wrist joint, from the joint part options preset by the interactive device through the liquid crystal touch panel 1 of the interactive device. After receiving the information selected by the user, the corresponding instructions are sent to the ultrasonic detection unit.

[0062] The ultrasonic transducer in the ultrasonic detection unit starts working, emitting ultrasonic waves to the target joint in a sector scanning mode, and rotating according to a preset angle range (such as 60°-120°) to ensure that the ultrasonic waves can cover most areas of the target joint. While emitting ultrasonic waves, the ultrasonic transducer also receives echo signals from the joint tissue; the echo signal passes through the signal amplification circuit in the ultrasonic detection unit to amplify the weak electrical signal to a processable intensity, and then the noise interference in the echo signal is removed by the filtering circuit to improve the quality of the echo signal. The processed echo signal is received and, according to the different echo intensities, the echo signal is accurately mapped from the electrical signal to the grayscale information in the image to generate an initial ultrasonic grayscale image; through the sector scanning mode, the ultrasonic echo signal of the target joint can be fully acquired, and the generated initial ultrasonic grayscale image can intuitively display the general morphology and structure of the joint tissue, providing basic data for subsequent processing.

[0063] Furthermore, the sub-logic for determining the target detection area includes:

[0064] Preprocessing and edge detection are performed on the initial ultrasonic grayscale image to identify the edge points of the joint cavity boundary, and curve fitting is performed on the edge points to obtain the joint cavity boundary;

[0065] The ultrasound grayscale image is registered with the standard joint image through a feature-based image registration algorithm, and the synovium and articular cartilage are segmented from the ultrasound grayscale image.

[0066] The target detection area is determined based on the recognition results of the joint cavity boundary and the segmentation results of the synovium and articular cartilage.

[0067] In order to detect the inflammation area more accurately, it is necessary to clarify the target detection area, eliminate the interference of irrelevant tissues, and improve the pertinence and accuracy of the detection; the initial ultrasonic grayscale image is preprocessed, and the median filtering algorithm is first used to remove the salt and pepper noise in the ultrasonic grayscale image. The median filtering algorithm can effectively suppress noise while retaining the edge information of the ultrasonic grayscale image by selecting the median of the pixel value in the local area of ​​the ultrasonic grayscale image. The Canny edge detection algorithm is then used to detect the edge of the preprocessed ultrasonic grayscale image. The Canny algorithm calculates the gradient amplitude and gradient direction of the ultrasonic grayscale image and sets the grayscale threshold to screen the edge points, which can accurately detect the edge points of the joint cavity boundary; the detected edge points are used as input, and curve fitting is performed by the least squares method to obtain a smooth curve, which is the joint cavity boundary. During the fitting process, some prior knowledge, such as the approximate shape and range of the joint cavity boundary, is combined to optimize the fitting results and improve the accuracy of the boundary.

[0068] The ultrasound grayscale image is registered with the standard joint image built into the device through a feature-based image registration algorithm, such as the SIFT algorithm. The SIFT algorithm extracts key points and feature descriptors from the ultrasound grayscale image and finds matching points between the two images, thereby achieving image registration. After image registration, the synovium and articular cartilage are segmented from the ultrasound grayscale image based on the grayscale features of the synovium and articular cartilage in the ultrasound grayscale image through a threshold segmentation-based algorithm. For example, by setting an appropriate grayscale threshold, pixels with grayscale values ​​within the grayscale threshold range are classified as synovial membrane or articular cartilage tissue.

[0069] Based on the recognition results of the joint cavity boundary and the segmentation results of the synovium and articular cartilage, a comprehensive judgment is made to determine the target detection area, focusing on areas prone to inflammation such as the junction of the synovium and articular cartilage and the inside of the joint cavity. By delineating rectangular boxes or polygonal areas, the scope of the target detection area is clarified, thereby accurately determining the target detection area, which can reduce the amount of data for subsequent detection, improve detection efficiency, avoid interference of irrelevant tissues on the detection results, and improve detection accuracy.

[0070] Joint tissues at different depths will have varying degrees of inflammation. Layered testing can provide a more comprehensive and detailed understanding of the internal conditions of the joint, thereby improving detection accuracy. Based on the depth information of the target joint, the number of detection layers and the thickness of each layer are calculated. For example, for a knee joint with a depth of 3-5cm, it is divided into 3-5 layers, with each layer about 1cm thick. The determination of the detection layers takes into account the penetration ability and resolution requirements of ultrasound in different tissues to ensure that sufficiently detailed information can be obtained.

[0071] For different detection layers, the ultrasonic detection unit automatically adjusts the ultrasonic transmission frequency. Generally speaking, for shallower detection layers, a higher transmission frequency, such as 5-10MHz, is used to obtain higher resolution; for deeper detection layers, a lower transmission frequency, such as 2-5MHz, is used to ensure that the ultrasonic wave can penetrate to the corresponding depth. The adjustment of the transmission frequency is achieved by changing the driving signal frequency of the ultrasonic transducer.

[0072] Within the target detection area of ​​each detection layer, the ultrasonic transducer scans according to a spiral progressive scanning path, starting from the center of the target detection area and gradually expanding the scan outward in a spiral manner. This scanning path can ensure a comprehensive and complete scanning of the target detection area, while avoiding repeated scanning and missed areas. During the scanning process, the ultrasonic transducer continuously transmits and receives ultrasonic waves, and records the ultrasonic attenuation coefficient of each detection layer in real time. It also records information including the ultrasonic emission frequency, emission intensity, and echo intensity of different detection layers. Through layered scanning and targeted frequency adjustment, detailed ultrasonic data of joint tissues at different depths can be obtained, thereby improving the detection accuracy of the internal structure of the joint and inflammation.

[0073] Specifically, the logic for obtaining the ultrasonic attenuation coefficient includes:

[0074] Record the ultrasound emission frequency and emission intensity, and record the echo intensity of different detection layers;

[0075] Perform distance correction on the echo intensities of different detection layers to obtain the corrected echo intensities;

[0076] The ultrasonic attenuation coefficients of different detection layers are calculated based on the ultrasonic emission intensity, the corrected echo intensity, and the propagation distances of different detection layers.

[0077] The ultrasonic attenuation coefficient can reflect the absorption and scattering of ultrasound by joint tissue and is an important basis for determining the location and extent of inflammation. During the scanning process, accurately recording the ultrasound emission frequency and emission intensity, as well as the echo intensity of different detection layers, can ensure the accuracy and real-time nature of the relevant data.

[0078] Since the intensity of ultrasound waves will attenuate as the propagation distance increases during the propagation process, it is necessary to perform distance correction on the echo intensity. The distance correction is based on the propagation speed v of ultrasound waves in human tissue and the time interval Δt between transmitting and receiving ultrasound waves. i , calculate the propagation distance d of each detection layer i , where d i =v×Δt i / 2, round trip propagation needs to be taken into account; then the echo intensity is corrected to obtain the corrected echo intensity I i .

[0079] Based on the ultrasonic emission intensity, the corrected echo intensity, and the propagation distance of different detection layers, the ultrasonic attenuation coefficient of different detection layers is calculated. The functional expression of the ultrasonic attenuation coefficient of different detection layers is as follows:

[0080]

[0081] Where, α i represents the ultrasonic attenuation coefficient of the i-th detection layer, d i represents the propagation distance of the i-th detection layer, I i It represents the echo intensity after the i-th detection layer correction, and I0 represents the ultrasonic emission intensity.

[0082] The accurately calculated ultrasonic attenuation coefficient can intuitively reflect the health status of joint tissue and provide a quantitative basis for subsequent judgment of the location and extent of inflammation.

[0083] Displaying the ultrasonic attenuation coefficient in the form of an image can more intuitively present the attenuation conditions of different areas inside the joint, making it easier for doctors or operators to determine the location and range of inflammation; the ultrasonic attenuation coefficients of multiple detection layers are fused, and the fused numerical form is expressed as the average of the ultrasonic attenuation coefficients of multiple detection layers. The discrete ultrasonic attenuation coefficient is converted into continuous image data through an interpolation algorithm. For example, through a bilinear interpolation algorithm, the ultrasonic attenuation coefficients of other positions in the image are calculated based on the ultrasonic attenuation coefficients of adjacent detection points, and then these ultrasonic attenuation coefficients are mapped to different grayscale values ​​or color values ​​to generate a joint ultrasonic attenuation distribution map. When generating the joint ultrasonic attenuation distribution map, a suitable color mapping table can be set according to actual needs so that different ranges of ultrasonic attenuation coefficients correspond to different colors, which is convenient for observation and analysis.

[0084] According to the pre-set normal ultrasonic attenuation coefficient range, the area beyond the normal ultrasonic attenuation coefficient range is marked as the abnormal attenuation area. On the joint ultrasonic attenuation distribution map, the abnormal attenuation area can be marked with red or other eye-catching colors. At the same time, the relevant information of the abnormal attenuation area, such as the position and area of ​​the abnormal attenuation area, can be displayed next to the joint ultrasonic attenuation distribution map or through a pop-up window; thereby, the ultrasonic attenuation inside the joint can be clearly and intuitively displayed. The marking of the abnormal attenuation area can quickly locate the site of inflammation, providing an important reference for subsequent treatment.

[0085] The intelligent adjustment unit is used to determine the location, area and degree of inflammation based on the joint ultrasonic attenuation distribution map, generate interference electrical parameters, and arrange the interference electrical combination according to the interference electrical parameters so that the interference electrical directional output acts on the inflammation location of the target joint.

[0086] Specifically, the logic for determining the location, area, and degree of inflammation includes:

[0087] Receive the joint ultrasound attenuation distribution map and preliminarily screen out abnormal attenuation areas through threshold segmentation;

[0088] Based on morphological operations, adjacent abnormal attenuation areas are connected to form the outline of the inflammation area;

[0089] The center coordinates of the inflammation area were calculated using the centroid algorithm and marked as the inflammation location;

[0090] Count the total number of pixels in the inflammation area to obtain the inflammation area;

[0091] The degree of inflammation was determined based on the mean value of the ultrasound attenuation coefficient within the inflamed area.

[0092] Clarifying the specific location, area and degree of inflammation provides a key basis for the subsequent precise formulation of interferometric electrical treatment plans to achieve personalized and effective treatment; obtaining the generated joint ultrasonic attenuation distribution map from the ultrasonic detection unit, the joint ultrasonic attenuation distribution map is stored in the form of a digital image, and contains ultrasonic attenuation coefficient information of different areas; through the threshold segmentation method in the image processing algorithm, such as the Otsu algorithm, the Otsu algorithm can automatically calculate an optimal threshold, and compare the pixel points in the joint ultrasonic attenuation distribution map with the optimal threshold according to their corresponding ultrasonic attenuation coefficient. Pixel points greater than or equal to the optimal threshold are screened out, and abnormal attenuation areas are preliminarily screened out.

[0093] Morphological operations are performed on the screened abnormal attenuation areas, mainly including dilation and erosion operations. The dilation operation can connect adjacent abnormal attenuation areas with small gaps by expanding the edge pixels of the abnormal attenuation area outward, while the erosion operation removes isolated noise points in the abnormal area. After multiple alternating dilation and erosion operations, a continuous and complete outline of the inflammation area is formed.

[0094] The contoured inflammation area is regarded as a two-dimensional plane figure, and the center coordinates of the inflammation area are calculated using the centroid algorithm. The mathematical principle of the centroid algorithm is based on the coordinates of all pixel points in the area and the corresponding weights (the weight can be set to 1, that is, each pixel point contributes the same to the centroid calculation). The centroid coordinates are obtained through the existing calculation formula. The centroid coordinates are the marked position of the inflammation position in the ultrasonic attenuation distribution map.

[0095] Traverse all the pixels in the inflamed area and count the total number of pixels. Since each pixel in the joint ultrasound attenuation distribution map corresponds to a certain area of ​​the actual joint part (determined by the scale of the ultrasound grayscale image), the total number of pixels is multiplied by the actual area corresponding to a single pixel to obtain the inflamed area.

[0096] The ultrasonic attenuation coefficients corresponding to all pixels in the inflammation area are extracted, the average value of the ultrasonic attenuation coefficients corresponding to all pixels is calculated, the minimum threshold and maximum threshold are configured and compared with the average value of the ultrasonic attenuation coefficients corresponding to all pixels to determine the current degree of inflammation, such as mild inflammation, moderate inflammation or severe inflammation, where mild inflammation means that the average value of the ultrasonic attenuation coefficients corresponding to all pixels is between 0 and the minimum threshold, and severe inflammation means that the average value of the ultrasonic attenuation coefficients corresponding to all pixels is greater than the maximum threshold. This allows the key information of inflammation to be extracted more accurately from the ultrasonic attenuation distribution map, providing quantitative and precise data support for the subsequent formulation of interferential electrical therapy plans.

[0097] Specifically, if Figure 4 As shown, the generation logic of interference electrical parameters includes:

[0098] Interference electrical parameters include the amplitude, frequency and waveform of interference electricity. The amplitude of interference electricity is generated according to the degree of inflammation and the area of ​​inflammation.

[0099] Determine the detection layer where the inflammation area is located to dynamically adjust the frequency of the interference electricity and determine the waveform of the interference electricity;

[0100] The ultrasonic attenuation coefficient is updated after the interfering electrical parameters act on the inflammation position, and the amplitude of the interfering electrical current is adjusted according to the decreasing rate of the ultrasonic attenuation coefficient.

[0101] Appropriate interference electrical parameters are generated according to the specific situation of inflammation, so that the interference electricity can act more effectively on the inflamed area and improve the treatment effect; the amplitude of the interference electricity is generated according to the degree of inflammation (the average value of the ultrasonic attenuation coefficient corresponding to all pixel points) and the area of ​​inflammation. Generally speaking, the more severe the inflammation and the larger the area of ​​inflammation, the higher the output interference electricity amplitude.

[0102] Determine the detection layer information where the inflammation area is located. This detection layer information is obtained from the ultrasonic detection unit. Different detection layers have different responses to the interference electrical frequency due to different tissue characteristics and depths. For example, shallower detection layers are more sensitive to higher-frequency interference electricity, while deeper layers require lower-frequency interference electricity to ensure penetration. At the same time, according to the degree of inflammation and the treatment stage, select the appropriate interference electrical waveform. For example, square waves are suitable for stronger stimulation, while sine waves are relatively mild and can be switched according to actual conditions.

[0103] Furthermore, the sub-logic for adjusting the amplitude of the interference voltage includes:

[0104] The amplitude of the interference current is calculated and adjusted according to the decrease rate of the ultrasonic attenuation coefficient;

[0105] applying the adjusted amplitude of the interfering electricity to the interfering electricity to direct the output toward the inflammation site;

[0106] The rate of decrease of the ultrasonic attenuation coefficient and the amplitude of the interference electricity are continuously monitored to trigger early warning processing.

[0107] After the generated interfering electrical parameters are applied to the inflammation site, the ultrasonic detection unit detects the joint site again, obtains a new ultrasonic attenuation coefficient, and calculates the decrease rate of the ultrasonic attenuation coefficient, that is, (initial ultrasonic attenuation coefficient - new ultrasonic attenuation coefficient) / initial ultrasonic attenuation coefficient. The adjusted interfering electrical amplitude is calculated according to the calculation formula for adjusting the interfering electrical amplitude; the generated interfering electrical parameters can better match the specific situation of the inflammation and improve the pertinence and effectiveness of interfering electrical treatment.

[0108] The calculation formula for adjusting the amplitude of the interference voltage is as follows:

[0109] C new =C before ×(1+k×η);

[0110] Where C new Indicates the amplitude of the adjusted interference voltage, C before represents the amplitude of the interference current before adjustment, k represents the adjustment coefficient, k needs to be optimized according to the actual treatment effect and patient feedback, 0<k<1, η represents the decrease rate of the ultrasonic attenuation coefficient.

[0111] Specifically, the logic that interferes with the electrical directional output includes:

[0112] Determine the electrode combination layout according to the location of inflammation, and monitor the tissue impedance when the electrodes are in contact with the skin in real time;

[0113] According to the generated interference electrical parameters and the electrode combination layout, the phase difference between the electrode combinations is calculated;

[0114] According to the phase difference between the electrode combinations, the interference electricity forms an electric field distribution in space, focusing on the inflammation site for directional output;

[0115] During the process of interfering electrical directional output, the change data of tissue impedance and ultrasonic attenuation coefficient are monitored in real time to determine whether to dynamically adjust the phase difference between the electrode combinations and the interfering electrical parameters.

[0116] Achieve directional output of interference electricity so that the interference electricity can be concentrated on the inflammation site, improve the treatment effect, and reduce the impact on the surrounding normal tissues. According to the determined inflammation site, select a suitable electrode combination in the electrode array of the interactive device. For example, if the inflammation site is on one side of the joint, select the electrode close to that side, and determine the optimal spacing and arrangement between the electrodes to ensure that the interference electricity can be focused on the inflammation site; set an impedance sensor at the contact point between the electrode and the skin. The impedance sensor measures the tissue impedance between the electrode combination and the skin in real time, and transmits the measurement data to the intelligent adjustment unit. The change in tissue impedance can reflect the contact status between the electrode and the skin and the physiological changes inside the tissue.

[0117] Based on the generated interference electrical parameters, including the frequency of the interference electrical current, the wavelength of the interference electrical current is determined. Combined with the information of the electrode combination layout (the interval between the electrode combinations) and the angle between the center coordinates of the inflammation area and the electrode connection line, the phase difference between the electrode combinations is calculated. The calculation formula for the phase difference between the electrode combinations is as follows:

[0118]

[0119] Where, represents the phase difference between the electrode combinations, h represents the interval between the electrode combinations, λ represents the wavelength of the interference electricity, and θ represents the angle between the center coordinate of the inflammation area and the electrode connection line.

[0120] Based on the calculated phase difference between the electrode combinations, the time sequence of the electrodes outputting interfering electrical signals is controlled. By precisely controlling the phase of the output signal of each electrode, the interfering electricity forms a specific electric field distribution in space. This electric field can be focused on the location of inflammation, thereby achieving directional output of interfering electricity.

[0121] During the directional output of interference electricity, the change data of tissue impedance and ultrasonic attenuation coefficient are continuously monitored. If the tissue impedance suddenly increases, the intelligent adjustment unit will issue an alarm to remind the operator that there is poor contact between the electrode and the skin. The operator can adjust the position of the electrode or increase the contact pressure according to the prompt; at the same time, according to the change of the ultrasonic attenuation coefficient, it is judged whether the interference electricity parameters need to be adjusted. For example, if the ultrasonic attenuation coefficient decreases slowly, it means that the treatment effect is not good, and the amplitude, frequency or waveform of the interference electricity needs to be adjusted; thereby achieving precise directional output of interference electricity and improving the treatment effect. At the same time, according to real-time feedback during the treatment process, the interference electricity parameters can be adjusted in time to ensure the safety and effectiveness of the treatment.

[0122] Furthermore, the sub-logic for adjusting the phase difference between the electrode combinations includes:

[0123] Determine the phase delay caused by tissue impedance and determine the phase compensation value;

[0124] The phase difference between the electrode combinations is recalculated based on the phase compensation value.

[0125] During interferential electrical therapy, changes in factors such as tissue impedance will cause deviations in the actual phase difference between the electrode combinations, which require adjustments to ensure the directional focusing effect of the interferential electricity. The intelligent adjustment unit determines the phase delay caused by changes in tissue impedance based on the real-time monitored tissue impedance data. For example, when tissue impedance increases, the signal transmission speed will slow down, resulting in an increase in phase delay.

[0126] Based on the judgment result of the phase delay, the phase compensation value is calculated, where the phase compensation value and the phase delay are the inverse of each other, and the phase difference between the electrode combinations is recalculated, and then the phase of the electrode output signal is adjusted according to the new phase difference; thereby, the phase deviation caused by factors such as changes in tissue impedance can be corrected in a timely manner, ensuring that the interference electricity can always be accurately focused on the inflammation location in space, thereby improving the stability of the treatment effect.

[0127] Specifically, the formula for recalculating the phase difference between electrode combinations based on the phase compensation value is as follows:

[0128]

[0129] Where, represents the phase difference between the electrode combinations recalculated according to the phase compensation value, h represents the interval between the electrode combinations, λ represents the wavelength of the interference electricity, θ represents the angle between the center coordinate of the inflammation area and the electrode connection line, and φ represents the phase compensation value.

[0130] The operation process of this device is as follows: after the interactive device is turned on, the user enters the patient's basic information through the LCD touch panel 1;

[0131] Attach the adsorption electrodes or self-adhesive electrodes to the patient's joints, ensuring close contact between the electrodes and the skin;

[0132] Start the ultrasonic detection unit to detect the joint, obtain the ultrasonic attenuation coefficient and transmit it to the intelligent adjustment unit;

[0133] The intelligent adjustment unit analyzes and processes the ultrasonic attenuation coefficient to determine the inflammation of the joint and adaptively adjusts the interference electrical parameters based on the determination results.

[0134] The user can fine-tune the output intensity of the interference power according to his or her own feelings through the output intensity adjustment button 3;

[0135] The device status indicator 4 displays the working status of the device in real time, such as power status and treatment status;

[0136] After the treatment is completed, the user can view the treatment record through the LCD touch panel 1.

Claims

1. An interfering electrical device for assisting in the treatment of arthritis, characterized in that: include: Detection and adjustment module, which includes an ultrasonic detection unit and an intelligent adjustment unit; The ultrasonic detection unit is used to detect the target joint part through ultrasound, identify the boundary of the joint cavity and segment the synovium and articular cartilage, determine the detection layer based on the depth of the target joint part and scan it, obtain the ultrasonic attenuation coefficient of different detection layers, and generate the joint ultrasonic attenuation distribution map after fusion; The intelligent adjustment unit is used to determine the location, area and degree of inflammation based on the joint ultrasonic attenuation distribution map, generate interference electrical parameters, and arrange the interference electrical combination according to the interference electrical parameters so that the interference electrical directional output acts on the inflammation location of the target joint.

2. The interfering electrical device for assisting in the treatment of arthritis according to claim 1, characterized in that: The detection logic of the target joint part includes: Select the target joint area, apply ultrasound to cover the target joint area in a sector scanning mode, and generate an initial ultrasound grayscale image based on the ultrasound echo intensity; The joint cavity boundary is identified based on the initial ultrasound grayscale image, and the synovium and articular cartilage are segmented through image registration algorithm to determine the target detection area; Determine the detection layer according to the depth of the target joint, adjust the ultrasound transmission frequency based on the detection layer, and scan the target detection area of ​​each detection layer through a spiral progressive scanning path to obtain the ultrasound attenuation coefficient of each detection layer; The ultrasound attenuation coefficients of multiple detection layers are fused in real time to generate a joint ultrasound attenuation distribution map and mark abnormal attenuation areas.

3. The interfering electrical device for assisting in the treatment of arthritis according to claim 2, characterized in that: The target detection area determination sub-logic includes: Preprocessing and edge detection are performed on the initial ultrasonic grayscale image to identify the edge points of the joint cavity boundary, and curve fitting is performed on the edge points to obtain the joint cavity boundary; The ultrasound grayscale image is registered with the standard joint image through a feature-based image registration algorithm, and the synovium and articular cartilage are segmented from the ultrasound grayscale image. The target detection area is determined based on the recognition results of the joint cavity boundary and the segmentation results of the synovium and articular cartilage.

4. The interfering electrical device for assisting in the treatment of arthritis according to claim 3, characterized in that: The logic for obtaining the ultrasonic attenuation coefficient includes: Record the ultrasound emission frequency and emission intensity, and record the echo intensity of different detection layers; Perform distance correction on the echo intensities of different detection layers to obtain the corrected echo intensities; The ultrasonic attenuation coefficients of different detection layers are calculated based on the ultrasonic emission intensity, the corrected echo intensity, and the propagation distances of different detection layers.

5. The interfering electrical device for assisting in the treatment of arthritis according to claim 4, characterized in that: The logic for determining the inflammation location, inflammation area, and inflammation degree includes: Receive the joint ultrasound attenuation distribution map and preliminarily screen out abnormal attenuation areas through threshold segmentation; Based on morphological operations, adjacent abnormal attenuation areas are connected to form the outline of the inflammation area; The center coordinates of the inflammation area were calculated using the centroid algorithm and marked as the inflammation location; Count the total number of pixels in the inflammation area to obtain the inflammation area; The degree of inflammation was determined based on the mean value of the ultrasound attenuation coefficient within the inflamed area.

6. The interfering electrical device for assisting in the treatment of arthritis according to claim 5, characterized in that: The generation logic of the interference electrical parameters includes: Interference electrical parameters include the amplitude, frequency and waveform of interference electricity. The amplitude of interference electricity is generated according to the degree of inflammation and the area of ​​inflammation. Determine the detection layer where the inflammation area is located to dynamically adjust the frequency of the interference electricity and determine the waveform of the interference electricity; The ultrasonic attenuation coefficient is updated after the interfering electrical parameters act on the inflammation position, and the amplitude of the interfering electrical current is adjusted according to the decreasing rate of the ultrasonic attenuation coefficient.

7. The interfering electrical device for assisting in the treatment of arthritis according to claim 6, characterized in that: The sub-logic for adjusting the amplitude of the interference current includes: The amplitude of the interference current is calculated and adjusted according to the decrease rate of the ultrasonic attenuation coefficient; applying the adjusted amplitude of the interfering electricity to the interfering electricity to direct the output toward the inflammation site; The rate of decrease of the ultrasonic attenuation coefficient and the amplitude of the interference electricity are continuously monitored to trigger early warning processing.

8. The interfering electrical device for assisting in the treatment of arthritis according to claim 7, characterized in that: The logic of the interference electrical directional output includes: Determine the electrode combination layout according to the location of inflammation, and monitor the tissue impedance when the electrodes are in contact with the skin in real time; According to the generated interference electrical parameters and the electrode combination layout, the phase difference between the electrode combinations is calculated; According to the phase difference between the electrode combinations, the interference electricity forms an electric field distribution in space, focusing on the inflammation site for directional output; During the process of interfering electrical directional output, the change data of tissue impedance and ultrasonic attenuation coefficient are monitored in real time to determine whether to dynamically adjust the phase difference between the electrode combinations and the interfering electrical parameters.

9. The interfering electrical device for assisting in the treatment of arthritis according to claim 8, characterized in that: The sub-logic for adjusting the phase difference between the electrode combinations includes: Determine the phase delay caused by tissue impedance and determine the phase compensation value; The phase difference between the electrode combinations is recalculated based on the phase compensation value.

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