A pelvic floor muscle pressure detection device and system

Abstract

The present application provides a pelvic floor muscle pressure detection device and system, belonging to the field of medical device technology. The device includes: a probe, including a flexible housing and an ion-type pressure sensor array, the ion-type pressure sensor array is arranged on the inner surface of the flexible housing, and is used to detect the pelvic floor muscle pressure of the object under test when the probe is inserted into the cavity of the object under test, and convert the pelvic floor muscle pressure into a sensing capacitance signal; a handle, connected to the probe, the handle is provided with a signal processing module, the signal processing module is electrically connected to the ion-type pressure sensor array, and is used to convert the sensing capacitance signal into a detection voltage signal based on the capacitance value of the adjusted reference capacitor under the action of a positive excitation voltage and a negative excitation voltage, and obtain the pelvic floor muscle pressure value of the object under test based on the detection voltage signal, wherein the capacitance value of the reference capacitor is configured to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than a first threshold. The present application can improve the accuracy of pelvic floor muscle pressure detection within a small pressure range.

Description

Technical Field

[0001] The present application relates to the field of medical device technology, and in particular to a pelvic floor muscle pressure detection device and system. Background Art

[0002] Pelvic floor muscle testing is a medical examination that is mainly used to evaluate the function of the pelvic floor muscles. The pelvic floor muscles are a group of muscles located at the bottom of the pelvis that are responsible for supporting the bladder, uterus and rectum. Through pelvic floor muscle testing, pelvic floor muscle dysfunction, such as urinary incontinence and pelvic organ prolapse, can be diagnosed and evaluated. Pelvic floor dysfunction is a pathological change in the pelvic floor tissue structure caused by damage to the pelvic floor support structure, congenital defects and degenerative factors, including a decrease in the strength of the pelvic floor muscles such as connective tissue, muscles and ligaments.

[0003] In clinical practice, electromyographic biosignal detectors are often used to assess pelvic floor muscle strength. This detector inserts a vaginal electromyographic probe into the vagina and collects vaginal surface electromyographic signals to observe the physiological changes during pelvic floor muscle contraction, thus providing an important basis for the diagnosis and treatment of pelvic floor dysfunction. However, vaginal electromyographic signals are easily affected by a variety of factors, including local tissue characteristics, crosstalk, electrode placement location and depth, etc., all of which can lead to inconsistent test results.

[0004] In order to improve the accuracy of the test results, there is currently a technology that proposes to apply capacitive pressure sensors to pelvic floor muscle detection. However, in terms of pressure sensing technology, it is still simply a simple appropriation of existing technology. Capacitive pressure sensing arrays, including existing capacitive pressure sensors, usually have poor linear response and sensitivity to parasitic capacitance and edge capacitance, and the detection accuracy of pelvic floor muscle pressure within a small pressure range is not ideal. Summary of the invention

[0005] The purpose of this application is to provide a pelvic floor muscle pressure detection device and system to solve the above problems.

[0006] To achieve the above objectives, the present application proposes a pelvic floor muscle pressure detection device, which includes:

[0007] A probe, the probe comprising a flexible housing and an ion-type pressure sensor array, the ion-type pressure sensor array being arranged on the inner surface of the flexible housing in the form of an array of m rows and n columns, for detecting the pelvic floor muscle pressure of the subject when the probe is inserted into the cavity of the subject, and converting the pelvic floor muscle pressure into a sensing capacitance signal, wherein m and n are integers greater than or equal to 1;

[0008] A handle, wherein the handle is connected to the probe, and the handle is provided with a signal processing module, wherein the signal processing module is electrically connected to the ion-type pressure sensor array, and the signal processing module is used to convert the sensing capacitance signal generated by the ion-type pressure sensor array into a detection voltage signal under the action of a positive excitation voltage and a negative excitation voltage based on adjusting the capacitance value of a reference capacitor, and obtain the pelvic floor muscle pressure value of the object under test based on the detection voltage signal, wherein the capacitance value of the reference capacitor is configured to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than a first threshold.

[0009] In one embodiment, the ion-type pressure sensor array is evenly spaced and arranged on the inner surface of the flexible housing in the form of an array of m rows and n columns.

[0010] In one embodiment, the ion-type pressure sensor array is arranged in an array form of m rows and n columns at uneven intervals on the inner surface of the flexible shell, wherein the arrangement density of the ion-type pressure sensor array in a first length region where the probe is close to the handle is greater than the arrangement density in a second length region where the probe is far from the handle.

[0011] In one embodiment, the flexible housing includes a tubular portion and a spherical portion located on the top of the tubular portion, and the ion-type pressure sensor array is disposed on the inner surfaces of the tubular portion and the spherical portion, respectively.

[0012] In one embodiment, the signal processing module includes a control unit and at least one capacitance-voltage conversion circuit;

[0013] The capacitance-to-pressure conversion circuit comprises an operational amplifier and the reference capacitor, wherein two ends of the reference capacitor are respectively connected to an inverting input terminal and an output terminal of the operational amplifier, wherein the inverting input terminal of the operational amplifier is configured to be connected to a detection terminal of an ion-type pressure sensor of a corresponding column in the ion-type pressure sensor array; the non-inverting input terminal of the operational amplifier is configured to alternately input the positive excitation voltage and the negative excitation voltage, and the output terminal of the operational amplifier is configured to output a first detection voltage and a second detection voltage corresponding to the positive excitation voltage and the negative excitation voltage, respectively, when a reference voltage is input to a driving terminal of an ion-type pressure sensor of a target row in the ion-type pressure sensor array;

[0014] The control unit is connected to the output end of the operational amplifier, and is used to calculate the capacitance value of the ion-type pressure sensor in the target row in the ion-type pressure sensor array based on the amplitudes of the positive excitation voltage and the negative excitation voltage, the first detection voltage and the second detection voltage, and the capacitance value of the reference capacitor, and convert the capacitance value of the ion-type pressure sensor in the target row into the pelvic floor muscle pressure value of the object being measured.

[0015] In one embodiment, the signal processing module includes a first multi-way selection unit and a second multi-way selection unit, the first multi-way selection unit is used to input a reference voltage to the driving end of the off-type pressure sensor in the target row; the second multi-way selection unit is used to connect the detection ends of at least one column of off-type pressure sensors in the off-type pressure sensor array to the inverting input end of at least one operational amplifier in sequence.

[0016] In one embodiment, the reference capacitor includes a reference capacitor group in which a plurality of sub-reference capacitors are connected in parallel, and each of the plurality of sub-reference capacitors is connected in series with a switch; the capacitance value of the reference capacitor is configured to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than a first threshold value, including: controlling the switch in series with at least one sub-reference capacitor connected in parallel in the reference capacitor group to be disconnected, thereby reducing the capacitance value of the reference capacitor group.

[0017] In one embodiment, the probe is connected to the handle by a snap-fitting manner. When the probe is connected to the handle, the ion-type pressure sensor array is triggered to be electrically connected to the signal processing module.

[0018] In one embodiment, the handle further comprises a probe release button assembly, and the probe release button assembly is used to separate the probe from the handle by pressing when the probe is connected to the handle.

[0019] In one embodiment, the handle also includes an indicator light and a USB data cable. The indicator light is disposed on the outer wall of the handle and is electrically connected to the signal processing module to indicate the pelvic floor muscle detection status; the USB data cable is electrically connected to the signal processing module to power the signal processing module and transmit the pelvic floor muscle pressure value of the subject to be measured to the electronic device.

[0020] In addition, to achieve the above-mentioned purpose, the present application also provides a pelvic floor muscle pressure detection system, which includes a pelvic floor muscle pressure detection device and an electronic device as described above, the pelvic floor muscle pressure detection device and the electronic device are communicatively connected, and the electronic device is used to receive the pelvic floor muscle pressure value of the object under test transmitted by the pelvic floor muscle pressure detection device, and generate a pelvic floor muscle pressure distribution view based on the pelvic floor muscle pressure value of the object under test.

[0021] Compared with the prior art, the beneficial effects of this application include:

[0022] The pelvic floor muscle pressure detection device of the present embodiment, on the one hand, can better fit the pelvic floor muscle of the object to be measured by the probe structure including a flexible shell and an ion-type pressure sensor array, ensure the close contact and detection point coverage of the sensor array and the pelvic floor muscle, and reduce the detection error caused by poor contact or incomplete detection area. Because the ion capacitive pressure sensor array has the characteristics of high sensitivity and fast response, it can accurately capture the pressure changes of each detection point of the pelvic floor muscle, and further improve the accuracy of the detection result. On the other hand, the signal processing module works under the action of the positive excitation voltage and the negative excitation voltage based on the capacitance value of the reference capacitor. First, by alternately applying the positive excitation voltage and the negative excitation voltage, the nonlinear error and parasitic capacitance interference of the capacitive pressure sensor array can be eliminated, and the accuracy of the pelvic floor muscle pressure detection is further improved, and the demand for high-precision pressure distribution measurement of the pelvic floor muscle is met. Second, by adjusting the capacitance value of the reference capacitor, the signal processing module can be optimized according to different detection requirements, especially in the range of small pressures, to provide higher sensitivity and better adaptability. At the same time, the device of the present application has a simple mechanical structure. On the basis of improving the accuracy of pelvic floor muscle pressure detection within a small pressure range, it also reduces the manufacturing cost, so that the pelvic floor muscle pressure detection device has significant economic benefits whether it is used in medical clinics or in personal home medical terminals to provide convenient pelvic floor muscle pressure detection. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required for use in the embodiments will be briefly introduced below. It should be understood that the following drawings only show certain embodiments of the present application and therefore should not be regarded as limiting the scope of the present application.

[0024] Figure 1 is a schematic structural diagram of a pelvic floor muscle pressure detection device according to a first embodiment of the present application;

[0025] Figure 2 is a three-dimensional isometric view of a pelvic floor muscle pressure detection device according to a first embodiment of the present application;

[0026] Figure 3 is a structural schematic diagram of an array of non-uniformly spaced ion-type pressure sensors in a pelvic floor muscle pressure detection device according to the first embodiment of the present application;

[0027] Figure 4 is a three-dimensional isometric view of an array of non-uniformly spaced ion-type pressure sensors in a pelvic floor muscle pressure detection device according to the first embodiment of the present application;

[0028] Figure 5 is a schematic diagram of the circuit structure of a signal processing module in a pelvic floor muscle pressure detection device according to the second embodiment of the present application;

[0029] Figure 6 is a schematic diagram of the principle of a capacitance-voltage conversion circuit according to the first embodiment of the present application;

[0030] Figure 7 is a schematic diagram of the principle of a capacitance-voltage conversion circuit according to the second embodiment of the present application;

[0031] Figure 8 is a schematic diagram of the circuit structure of a signal processing module in a pelvic floor muscle pressure detection device according to a third embodiment of the present application;

[0032] Fig. 9 is a schematic diagram of the connection between the pelvic floor muscle pressure detection device and the electronic device in the pelvic floor muscle detection system according to an embodiment of the present application;

[0033] Fig.10 is a schematic diagram of the structure of an electronic device involved in a pelvic floor muscle detection system according to an embodiment of the present application;

[0034] Fig.11 This is a pelvic floor muscle pressure distribution view generated by the pelvic floor muscle detection system according to an embodiment of the present application.

[0035] Description of the accompanying drawings: 10-pelvic floor muscle pressure detection device; 1-probe; 11-flexible housing; 12-ion-type pressure sensor array; 13-first multi-channel sensing unit; 14-second multi-channel sensing unit; 21-signal processing module; 211-capacitance-pressure conversion circuit; 212-control unit; 22-probe release button assembly; 23-indicator light; 3-USB data cable; 100-electronic device; 101-central processing unit (CPU); 102-read-only memory (ROM); 103-random access memory (RAM); 104-bus; 105-input / output (I / O) interface; 106-input part; 107-output part; 108-storage part; 109-communication part; 110-drive; 111-removable medium. DETAILED DESCRIPTION

[0036] In order to make the purpose, technical scheme and advantages of the present application clearer, the technical scheme in the embodiment of the present application will be clearly and completely described below in conjunction with the drawings of the embodiment of the present application. However, it should be understood that the described embodiments are only some exemplary embodiments of the present application, rather than all embodiments, and therefore the following detailed description of the embodiment of the present application is not intended to limit the scope of the present application for protection. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without making creative work belong to the scope of protection of the present application.

[0037] All terms (including technical and scientific terms) used in this application have the meanings commonly understood by those skilled in the art, unless otherwise defined. It should be noted that the terms used here should be interpreted as having a meaning consistent with the context of this specification, and should not be interpreted in an idealized or overly rigid manner.

[0038] For example, the terms "first", "second", etc. used in this application may be used herein to describe various features, but these features are not limited by these terms. These terms are only used to distinguish a first feature from another feature. For example, without departing from the scope of this application, a first detection voltage may be referred to as a second detection voltage, and similarly, a second detection voltage may be referred to as a first detection voltage. Both the first detection voltage and the second detection voltage are detection voltage signals, but they are not the same detection voltage signal.

[0039] For another example, the terms “include”, “comprising”, etc. used in this application indicate the existence of features, steps, operations and / or components, but do not exclude the existence or addition of one or more other features, steps, operations or components.

[0040] As mentioned above, the latest prior art proposes to apply capacitive pressure sensors to pelvic floor muscle detection, but in terms of pressure sensing technology, it is still simply misappropriating existing technology, and the capacitive pressure sensing array including the existing capacitive pressure sensor has poor linear response and sensitivity to parasitic capacitance and edge capacitance, which reduces the detection accuracy of the conventional capacitive sensing circuit based on the capacitive pressure sensor array for the sensing capacitance signal, and thus cannot meet the demand for high-precision pressure distribution measurement of the pelvic floor muscle. To this end, the present application proposes a pelvic floor muscle pressure detection device and system, which can improve the detection accuracy of the pelvic floor muscle pressure within a small pressure range and meet the demand for high-precision pressure distribution measurement of the pelvic floor muscle.

[0041] Figure 1 is a schematic structural diagram of a pelvic floor muscle pressure detection device 10 according to a first embodiment of the present application, Figure 2 3D is a perspective view of the pelvic floor muscle pressure detection device 10 according to the first embodiment of the present application. Figure 1 and Figure 2 As shown, the pelvic floor muscle pressure detection device 10 of this embodiment includes:

[0042] The probe 1 includes a flexible shell 11 and an ion-type pressure sensor array 12, which is arranged on the inner surface of the flexible shell 11 in the form of an array of m rows and n columns, and is used to detect the pelvic floor muscle pressure of the object under test when the probe 1 is inserted into the cavity of the object under test, and convert the pelvic floor muscle pressure into a sensing capacitance signal, where m and n are integers greater than or equal to 1.

[0043] A handle 2 is connected to the probe 1. The handle 2 is provided with a signal processing module 21. The signal processing module 21 is electrically connected to the ion-type pressure sensor array 12. The signal processing module 21 is used to convert the sensing capacitance signal generated by the ion-type pressure sensor array 12 into a detection voltage signal under the action of a positive excitation voltage and a negative excitation voltage based on adjusting the capacitance value of the reference capacitance (Cr1-Crn), and obtain the pelvic floor muscle pressure value of the object under test based on the detection voltage signal, wherein the capacitance value of the reference capacitance (Cr1-Crn) is configured to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than a first threshold.

[0044] In this embodiment, the flexible shell 11 refers to a shell made of a flexible material, such as silicone, thermoplastic elastomer (TPE), etc. It can be completely flexible or a structure with a certain degree of flexibility. The main feature of this shell is that it can bend and deform to a certain extent without breaking or being damaged, while maintaining its sealing and structural properties. In the pelvic floor muscle pressure detection device 10, the role of the flexible shell 11 is to provide an interface that contacts the pelvic floor muscle of the object being tested. Due to the complex anatomical structure of the pelvic floor muscle area and the large individual differences, the flexible shell 11 can better adapt to different physiological structures, provide a more comfortable detection experience, and ensure that the ionized pressure sensor array 12 can fit the pelvic floor muscle tightly, thereby improving the accuracy and reliability of the detection.

[0045] The flexible shell 11 made of medical grade flexible material not only has good biocompatibility, but also has certain strength and durability, and can withstand repeated use and disinfection. In some embodiments, the flexible shell 11 can be designed as a single-use product. Before each test, only a new flexible shell 11 needs to be replaced to ensure the sterility and accuracy of the device.

[0046] In one embodiment, the flexible shell 11 includes a tubular portion and a spherical portion located on the top of the tubular portion. In order to improve the accuracy of pelvic floor muscle pressure detection, this embodiment can respectively set the ionized pressure sensor array 12 on the inner surfaces of the tubular portion and the spherical portion, so that the pelvic floor muscle pressure detection device 10 can detect the pelvic floor muscle pressure at points in all directions contacted by the flexible shell 11, thereby ensuring the comprehensiveness and accuracy of the detection.

[0047] In this embodiment, the ion-type pressure sensor array 12 includes a sensor array composed of ion-capacitive pressure sensors. The ion-type pressure sensor array 12 includes an ion-film dielectric layer and an electrode array layer composed of m rows and n columns of electrodes. When the probe 1 is inserted into the cavity of the object to be measured, the pelvic floor muscle pressure of the object to be measured acts on the surface of the flexible shell 11, and the ion-film dielectric layer will deform, causing the capacitance between the electrodes to change, thereby converting the pelvic floor muscle pressure into a sensing capacitance signal.

[0048] In some embodiments, the ionization pressure sensor array 12 is evenly spaced in an array of m rows and n columns on the inner surface of the flexible housing 11. It is understood that the evenly spaced sensor array can provide more uniform pressure detection results and reduce the error of spatial resolution.

[0049] In some embodiments, reference Figure 3 and Figure 4 , the ion-type pressure sensor array 12 is arranged in an array form of m rows and n columns at uneven intervals on the inner surface of the flexible shell 11. In this case, the circuit design can be implemented by a sparse array of the ion-type pressure sensor array, that is, some rows and columns of sensor electrodes are left empty. Specifically, the arrangement density of the ion-type pressure sensor array 12 in the first length area of ​​the probe 1 close to the handle 2 is greater than the arrangement density in the second length area of ​​the probe 1 away from the handle 2. It can be understood that in the actual detection of the pelvic floor muscles, more emphasis may be placed on the pressure detection accuracy of the key points of the pelvic floor muscles of the subject being tested, and the non-uniformly spaced sensor array can provide higher detection accuracy in the key areas of the probe (such as some areas close to the handle), thereby further meeting the needs of high-precision detection of pelvic floor muscle pressure in different detection scenarios.

[0050] In some embodiments, the handle 2 is connected to the probe 1, and its connection method may include threaded connection, snap-on connection, etc. Preferably, in one embodiment, the probe 1 and the handle 2 are connected by snap-on connection, and the snap-on connection mainly relies on the cooperation of the buckle, the slot or the snap ring with the corresponding hole or slot to achieve the fixation and connection between the components. Furthermore, electrical connection contacts are designed at the connection part between the probe 1 and the handle 2. These contacts should be able to reliably contact when the probe 1 and the handle 2 are snap-on, so that when the probe 1 and the handle 2 are connected, the triggering off-type pressure sensor array 12 and the signal processing module 21 are electrically connected.

[0051] In this embodiment, the signal processing module 21 built into the handle 2 is a key component for realizing pelvic floor muscle pressure detection. It is electrically connected to the ion-type pressure sensor array 12, and based on the capacitance value of the adjusted reference capacitor (Cr1-Crn), the sensing capacitance signal generated by the ion-type pressure sensor array 12 is converted into a detection voltage signal under the action of the positive excitation voltage and the negative excitation voltage, thereby obtaining the pelvic floor muscle pressure value of the object being measured. After converting the sensing capacitance signal from the ion-type pressure sensor array 12 into a detection voltage signal, the signal processing module 21 obtains the sensing capacitance value of the ion-type pressure sensor corresponding to the detection voltage signal based on the analog-to-digital conversion calculation of the detection voltage signal, and obtains the true pressure value of the ion-type pressure sensor based on the pressure calibration function of the ion-type pressure sensor.

[0052] It should be understood that the signal processing module 21 in this embodiment works under the action of positive excitation voltage and negative excitation voltage. By alternately applying positive excitation voltage and negative excitation voltage, the signal processing module 21 can detect and obtain accurate sensing capacitance values ​​for the ion-type pressure sensor at each point in the ion-type pressure sensor array 12, thereby avoiding nonlinear errors caused by the poor linear response of the capacitive pressure sensor array and detection interference caused by parasitic capacitance and edge capacitance, thereby improving the accuracy of pelvic floor muscle pressure measurement.

[0053] The capacitance value of the reference capacitor (Cr1-Crn) in this embodiment is configured to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than the first threshold. The first threshold refers to a pre-set pressure value used to distinguish between a micro pressure range and a high pressure range. When the pelvic floor muscle pressure is lower than this threshold, it means that the pelvic floor muscle pressure is within a micro pressure range, and the capacitance change of the ion-type pressure sensor may be small. Therefore, the pelvic floor muscle pressure detection device requires higher sensitivity to detect tiny capacitance changes. By adjusting the capacitance value of the reference capacitor (Cr1-Crn) downward, the sensitivity of the pelvic floor muscle pressure detection device to capacitance changes within a micro pressure range can be increased, thereby improving the detection accuracy.

[0054] In some embodiments, the first threshold is a key parameter for defining the working mode of the pelvic floor muscle pressure detection device within different pressure ranges. When the detected pressure is lower than the first threshold, the pelvic floor muscle pressure detection device will enter a "high sensitivity" mode to more accurately capture and measure the pressure changes of the pelvic floor muscles.

[0055] In some embodiments, the handle 2 also includes a probe release button assembly 22, and the probe release button assembly 22 is used to separate the probe 1 from the handle 2 by pressing when the probe 1 is connected to the handle 2. In clinical applications, the probe 1 can be set to different sizes and different distributions of the ionizing pressure sensor array 12 according to the detection requirements of different objects to be tested, and these probes of different specifications can be quickly replaced and discarded as disposable components. Therefore, setting a probe release button assembly 22 that is convenient and quick to disassemble and replace the probe 1 can meet this demand. As a feasible installation method for a probe release button, the handle 2 is provided with a mounting hole on one side facing the probe 1, and the probe 1 is movably inserted in the mounting hole. A pressing hole is provided through the hole wall of the mounting hole, and the probe release button assembly 22 can be movably arranged along the hole depth direction of the pressing hole, and is buckled with the outer wall of the probe 1 to limit the movement of the probe.

[0056] In some embodiments, the handle 2 also includes an indicator light 23, which is disposed on the outer wall of the handle 2 and is electrically connected to the signal processing module 21 to indicate the pelvic floor muscle detection status, such as preparation, testing, detection completed, etc., and indications of abnormal conditions may also be considered, such as equipment failure, low battery, etc.

[0057] In some embodiments, the pelvic floor muscle pressure detection device 10 further includes a USB data line 3, which is electrically connected to the signal processing module 21 to power the signal processing module 21 and support the transmission of the pelvic floor muscle pressure value of the object being tested to the electronic device. The pelvic floor muscle pressure value is transmitted to the electronic device in a wired communication manner via the USB data line 3, which can be unaffected by wireless signal interference, provides a more stable connection, and is not prone to interruption or packet loss during data transmission.

[0058] In summary, the pelvic floor muscle pressure detection device 10 of the present embodiment can better fit the pelvic floor muscle of the object to be tested through the probe structure including the flexible housing 11 and the ion-type pressure sensor array 12, ensure the close contact and detection point coverage of the sensor array and the pelvic floor muscle, and reduce the detection error caused by poor contact or incomplete detection area. Since the ion-type pressure sensor array 12 has the characteristics of high sensitivity and fast response, it can accurately capture the pressure changes of each detection point of the pelvic floor muscle, further improving the accuracy of the detection result. On the other hand, the signal processing module 21 works under the action of the positive excitation voltage and the negative excitation voltage based on the adjustment of the capacitance value of the reference capacitor. First, by alternately applying the positive excitation voltage and the negative excitation voltage, the nonlinear error and parasitic capacitance interference of the ion-type pressure sensor array 12 can be eliminated, and the accuracy of the pelvic floor muscle pressure detection can be further improved, meeting the needs of high-precision pressure distribution measurement of the pelvic floor muscle. Second, by adjusting the capacitance value of the reference capacitor (Cr1-Crn), the signal processing module 21 can be optimized according to different detection requirements, especially in the small pressure range, to provide higher sensitivity and better adaptability. At the same time, the device of the present application has a simple mechanical structure, which not only improves the accuracy of pelvic floor muscle detection, but also reduces the manufacturing cost, so that the pelvic floor muscle pressure detection device 10 has significant economic benefits whether it is used in medical clinics or in personal home medical terminals to provide convenient pelvic floor muscle pressure detection.

[0059] Figure 5 2 is a schematic diagram of the circuit structure of the signal processing module 21 in the pelvic floor muscle pressure detection device 10 according to the second embodiment of the present application. Figure 5 As shown, the signal processing module 21 in the pelvic floor muscle pressure detection device 10 of this embodiment, based on any of the above-mentioned implementation modes, further includes: at least one capacitance-pressure conversion circuit 211 and a control unit 212.

[0060] Each capacitance-pressure conversion circuit 211 includes an operational amplifier (OA1-OAn) and a reference capacitor (Cr1-Crn), two ends of the reference capacitor (Cr1-Crn) are respectively connected to the inverting input terminal and the output terminal of the operational amplifier (OA1-OAn), the inverting input terminal of the operational amplifier (OA1-OAn) is configured to be connected to the detection terminal of the ion-type pressure sensor of the corresponding column in the ion-type pressure sensor array 12; the non-inverting input terminal of the operational amplifier (OA1-OAn) is configured to alternately input a positive excitation voltage and a negative excitation voltage, and the output terminal of the operational amplifier (OA1-OAn) is configured to output a first detection voltage and a second detection voltage corresponding to the positive excitation voltage and the negative excitation voltage, respectively, when a reference voltage is input to the driving terminal of the ion-type pressure sensor of the target row in the ion-type pressure sensor array 12;

[0061] The control unit 212 is connected to the output end of the operational amplifier (OA1-OAn), and is used to calculate the capacitance value of the ion-type pressure sensor in the target row in the ion-type pressure sensor array 12 based on the amplitude of the positive excitation voltage and the negative excitation voltage, the first detection voltage and the second detection voltage, and the capacitance value of the reference capacitor (Cr1-Crn), and convert the capacitance value of the ion-type pressure sensor in the target row into the pelvic floor muscle pressure value of the object being measured.

[0062] In this embodiment, the ion-type pressure sensor array 12 is arranged on the inner surface of the flexible housing 11 in the form of an array of m rows and n columns. According to the row, it can be represented as the first row C11-C1n, the second row C21-C2n, ..., the mth row Cm1-Cmn; according to the column, it can be represented as the first column C11-Cm1, the second column C12-Cm2, ..., the nth column C1n-Cmn. Each ion-type pressure sensor in each row of ion-type pressure sensors in the ion-type pressure sensor array 12 has a driving end and a detection end, wherein the driving end of each row of ion-type pressure sensors is connected to a driving voltage S0, and the driving voltage S0 is a fixed reference voltage Vref. In one embodiment, the driving end of each row of ion-type pressure sensors inputs the reference voltage Vref through at least one selection switch (SW1-SWm).

[0063] In this embodiment, each capacitance-pressure conversion circuit 211 includes an operational amplifier (OA1-OAn) and a reference capacitor (Cr1-Crn), and the two ends of the reference capacitor (Cr1-Crn) are respectively connected to the inverting input and output ends of the operational amplifier (OA1-OAn), and the inverting input end of the operational amplifier (OA1-OAn) is configured to be connected to the detection end of the ion-type pressure sensor of the corresponding column in the ion-type pressure sensor array 12. For example, for the capacitance-pressure conversion circuit 211 composed of the operational amplifier OA1 and the reference capacitor Cr1, the inverting input terminal of the operational amplifier OA1 is connected to the detection terminal of the first column of ion-type pressure sensors C11-Cm1; for the capacitance-pressure conversion circuit 211 composed of the operational amplifier OA2 and the reference capacitor Cr2, the inverting input terminal of the operational amplifier OA2 is connected to the detection terminal of the second column of ion-type pressure sensors C12-Cm2; and so on, for the capacitance-pressure conversion circuit 211 composed of the operational amplifier OAn and the reference capacitor Crn, the inverting input terminal of the operational amplifier OAn is connected to the detection terminal of the nth column of ion-type pressure sensors C1n-Cmn.

[0064] In the present embodiment, in each capacitance-pressure conversion circuit 211, an excitation voltage S1 is input to the non-phase input terminal of the operational amplifier (OA1-OAn), and the excitation voltage S1 is configured to alternately input a positive excitation voltage and a negative excitation voltage. Accordingly, the output terminal of the operational amplifier (OA1-OAn) is configured to output a first detection voltage and a second detection voltage corresponding to the positive excitation voltage and the negative excitation voltage, respectively, when a reference voltage is input to the driving terminal of the target row of the ion-type pressure sensor in the ion-type pressure sensor array 12. The first detection voltage and the second detection voltage can be detected by a control unit 212 connected to the output terminal of the operational amplifier (OA1-OAn). The control unit 212 can calculate the capacitance value of the ion-type pressure sensor in the target row in the ion-type pressure sensor array 12 with m rows and n columns based on the amplitudes of the positive excitation voltage and the negative excitation voltage, the first detection voltage and the second detection voltage, and the capacitance value of the reference capacitor (Cr1-Crn). The target row here refers to the currently selected row in the m-row n-column isoelectric pressure sensor array 12. At this time, the target row is in a selected state, and its driving end inputs the reference voltage Vref.

[0065] In some embodiments, the control unit 212 may include analog-to-digital conversion (ADC) channels of a number corresponding to the number of columns n of the m-row and n-column ion-type pressure sensor array 12, and the output terminals of the operational amplifiers (OA1-OAn) corresponding to each column are respectively connected to the corresponding analog-to-digital conversion (ADC) channels. Under the combined effect of the excitation voltage S1 input to the non-inverting input terminal of the operational amplifier (OA1-OAn) and the driving voltage S0 (i.e., the reference voltage Vref) input to the driving terminal of the ion-type pressure sensor of the target row, the first detection voltage and the second detection voltage output from the output terminal of the operational amplifier (OA1-OAn) are input to the analog-to-digital conversion (ADC) channel corresponding to the control unit 212, and the capacitance value of each ion-type pressure sensor of the target row is calculated after analog-to-digital conversion.

[0066] The calculation principle of the sensing calculation formula of the ionization pressure sensor can be combined with Figure 6 It is derived by the following formula:

[0067] like Figure 6 As shown, taking the capacitance-pressure conversion circuit 211 corresponding to the first column as an example, according to the virtual short principle of the operational amplifier, when the excitation voltage S1 input to the positive input terminal of the operational amplifier OA1 is changed, the voltage across the ionization pressure sensor C11 changes and charge transfer occurs. Since the leakage current of each pin of the operational amplifier OA1 is very small, the charge amount of the ionization pressure sensor C11 is basically the same as the charge amount of the reference capacitor Cr1. Assume that the charge amount of the ionization pressure sensor C11 is expressed as , the charge change of reference capacitor Cr1 is expressed as , then we can conclude .

[0068] Assume that the voltage change of the ionization pressure sensor C11 is expressed as , the capacitance value of the ionization pressure sensor C11 is expressed as , the voltage change of the reference capacitor Cr1 is expressed as , the capacitance value of the reference capacitor Cr1 is expressed as , then we can get formula (1):

[0069] (1).

[0070] Assuming that the reference voltage is represented by Vref, the amplitude of the forward excitation voltage input to the non-inverting input terminal of the operational amplifier OA1 is represented by , the amplitude of the negative excitation voltage is expressed as When the non-inverting input terminal of the operational amplifier OA1 first changes from the input reference voltage to the input forward excitation voltage for a predetermined time, the input voltage of the non-inverting input terminal of the operational amplifier OA1 changes from the reference voltage Vref to At this time, the first detection voltage corresponding to the forward excitation voltage at the output end of the operational amplifier OA1 is expressed as , then according to the above formula we can further get:

[0071] .

[0072] When the positive input terminal of the operational amplifier OA1 changes from the input reference voltage to the input negative excitation voltage for a predetermined time, the input voltage of the positive input terminal of the operational amplifier OA1 changes from the reference voltage Vref to At this time, the second detection voltage corresponding to the negative excitation voltage at the output terminal of the operational amplifier OA1 is expressed as , then according to the above formula we can further get:

[0073] .

[0074] Subtracting the above two formulas, we can further deduce:

[0075] ;

[0076] Thus, formula (2) can be obtained as follows:

[0077] (2).

[0078] It can be seen that the capacitance value of the ion-type pressure sensor C11 is highly correlated with the ratio of the difference between the first detection voltage and the second detection voltage to the sum of the amplitudes of the positive excitation voltage and the negative excitation voltage, and the capacitance value of the reference capacitor. Therefore, the control unit 212 can calculate the capacitance value of the ion-type pressure sensor in the target row in the m-row and n-column ion-type pressure sensor array 12 based on the amplitudes of the positive excitation voltage and the negative excitation voltage, the difference between the first detection voltage and the second detection voltage, and the capacitance value of the reference capacitor.

[0079] At the same time, it can be understood that when the capacitance value of the reference capacitor Cr1 is When it decreases, since the charges on both ends of formula (1) are equal, this will cause the voltage change of reference capacitor Cr1 to increase, resulting in an increase in the first detection voltage and the second detection voltage. In this way, even if the capacitance change of sensor C11 is very small, it can produce a large change in the sensing calculation, thereby improving the sensitivity and accuracy of pelvic floor muscle pressure detection in a small pressure range.

[0080] In one embodiment, if Figure 7As shown, the reference capacitor Cr1 in the capacitance-voltage conversion circuit 211 can be implemented by a reference capacitor group in which a plurality of sub-reference capacitors are connected in parallel, wherein each sub-reference capacitor connected in parallel in the reference capacitor group is respectively connected in series with a switch. Figure 7 The embodiment of the reference capacitor group including three sub-reference capacitors (Cr11, Cr12, Cr13) connected in parallel and switches (SW11, SW12, SW13) connected in series is only schematically shown. In fact, the number of sub-reference capacitors in the reference capacitor group can be appropriately set according to the sensitivity of the pelvic floor muscle pressure detection device to pressure sensing. In one embodiment, the switch can include an analog switch or a relay switch.

[0081] When the capacitance value of the reference capacitor (Cr1-Crn) is configured to need to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than the first threshold, thereby increasing the first detection voltage and the second detection voltage, the control unit 212 will output a switch on-off signal to change the switch connected in series with at least one of the multiple sub-reference capacitors connected in parallel in the reference capacitor group from connected to disconnected, thereby reducing the reference capacitance value of the reference capacitor group. For example, Figure 7 The switches connected in series to one or two of the three sub-reference capacitors (Cr11, Cr12, Cr13) are disconnected.

[0082] When the capacitance value of the reference capacitor (Cr1-Crn) is configured to need to be adjusted upward to adapt to the detection of pelvic floor muscle pressure greater than the first threshold value, thereby avoiding the overflow of the first detection voltage and the second detection voltage, the control unit 212 will output a switch on-off signal to change the switch connected in series with at least one of the multiple sub-reference capacitors connected in parallel in the reference capacitor group from disconnected to connected, thereby increasing the reference capacitance value of the reference capacitor group. For example, Figure 7 The switches connected in series to two or three of the three sub-reference capacitors (Cr11, Cr12, Cr13) are all connected.

[0083] The sensing calculation method of the ion-type pressure sensor of the control unit 212 can quickly and accurately calculate the capacitance value of the ion-type pressure sensor of the target row by alternately inputting a positive excitation voltage and a negative excitation voltage into the non-phase input terminal of the operational amplifier based on the amplitudes of the positive excitation voltage and the negative excitation voltage, the difference between the first detection voltage and the second detection voltage, and the capacitance value of the adjusted reference capacitor. This can significantly improve the detection accuracy of the pelvic floor muscle pressure detection device 10 for the pelvic floor muscle pressure within a small pressure range, and meet the needs of high-precision pressure distribution measurement in the pelvic floor muscle pressure detection scenario.

[0084] In this embodiment, the positive excitation voltage and the negative excitation voltage are symmetrical excitation voltages with the same excitation time, equal amplitude, and opposite polarity. By alternately inputting symmetrical excitation voltages with the same excitation time, equal amplitude, and opposite polarity to the positive phase input terminal of the operational amplifier (OA1-OAn), the order of inputting the positive excitation voltage and the negative excitation voltage can be arbitrarily exchanged, which can effectively avoid the polarization and electrolytic failure caused by the long-term DC bias of the ion-type pressure sensor in the ion-type pressure sensor array 12, and can significantly improve the service life and detection accuracy of the ion-type pressure sensor array 12.

[0085] Figure 8 is a schematic diagram of the circuit structure of the signal processing module 21 in the pelvic floor muscle pressure detection device 10 according to the third embodiment of the present application. Figure 8 As shown, the signal processing module 21 of this embodiment, based on any of the above-mentioned implementations, further includes: a first multi-way selection unit 13 and a second multi-way selection unit 14. The first multi-way selection unit 13 is used to input a reference voltage to the driving end of the ion-type pressure sensor of the target row; the second multi-way selection unit 14 is used to sequentially connect the detection end of at least one column of ion-type pressure sensors in the ion-type pressure sensor array 12 to the inverting input end of at least one operational amplifier (OA1-OAa).

[0086] In this embodiment, the first multi-way selection unit 13 is used to input a reference voltage to the driving end of the ion-type pressure sensor of the target row in a strobing manner. This design enables the pelvic floor muscle pressure detection device 10 to accurately control and switch the driving state of each sensor, thereby achieving efficient and accurate detection of pelvic floor muscle pressure and avoiding detection interference between sensors in different rows. By using the multi-way selection unit, the required hardware resources can be effectively reduced, the complexity of the system can be simplified, and the reliability and accuracy of the detection results can be guaranteed.

[0087] In this embodiment, the number a of the capacitive-pressure conversion circuits 211 depends on the number a of the analog-to-digital conversion (ADC) channels of the control unit 212. When the number a of the analog-to-digital conversion (ADC) channels of the control unit 212 is less than the number n of columns of the m-row and n-column ion-type pressure sensor array 12, that is, it is insufficient to meet the detection requirements of the ion-type pressure sensors in all columns of the m-row and n-column ion-type pressure sensor array 12, the detection ends of the n-column ion-type pressure sensors can be connected to the inverting input ends of the corresponding operational amplifiers (OA1-OAa) in a capacitive-pressure conversion circuit 211 in a sequentially selected manner through the second multiplexer 14.

[0088] For example, when the number of analog-to-digital conversion (ADC) channels of the control unit 212 is 1, the number of the capacitive-pressure conversion circuit 211 is 1, and the one capacitive-pressure conversion circuit 211 includes an operational amplifier (OA1). At this time, the second multiplexer selection unit 14 can connect the detection ends of all n columns of pressure sensing capacitors to the inverting input end of the operational amplifier (OA1) of the capacitive-pressure conversion circuit 211 in a sequentially selected manner; when the number of analog-to-digital conversion (ADC) channels of the control unit 212 is 2, the number of the capacitive-pressure conversion circuit 211 is 2, and the two capacitive-pressure conversion circuits 211 include operational amplifiers (OA1, OA2). At this time, the second multiplexer selection unit 14 can connect the detection ends of all n columns of pressure sensing capacitors to the inverting input end of the operational amplifier (OA1) of the capacitive-pressure conversion circuit 211 in a sequentially selected manner. The detection ends of every two columns of pressure sensing capacitors in the pressure sensing capacitors are connected to the inverting input ends of the operational amplifiers (OA1, OA2) of the capacitive-pressure conversion circuit 211 in a sequentially selected manner; similarly, by analogy, when the number of analog-to-digital conversion (ADC) channels of the control unit 212 is a, a is less than n, the number of the capacitive-pressure conversion circuits 211 is a, and the a capacitive-pressure conversion circuits 211 include operational amplifiers (OA1-OAa). At this time, the second multiplexing unit 14 can connect the detection ends of each a column of pressure sensing capacitors in all n columns of pressure sensing capacitors to the inverting input ends of the operational amplifiers (OA1-OAa) of the capacitive-pressure conversion circuit 211 in a sequentially selected manner.

[0089] It can be understood that when the number of analog-to-digital conversion (ADC) channels of the control unit 212 is n, the number of the capacitive-pressure conversion circuits 211 is n, and the n capacitive-pressure conversion circuits 211 include operational amplifiers (OA1-OAn). At this time, all the paths of the second multiplexer selection unit 14 are enabled, that is, the detection ends of all n columns of pressure sensing capacitors can be simultaneously connected to the inverting input ends of the operational amplifiers (OA1-OAn) of the n capacitive-pressure conversion circuits 211.

[0090] In addition, if Fig. 9 As shown, the embodiment of the present application also proposes a pelvic floor muscle pressure detection system, comprising a pelvic floor muscle pressure detection device 10 and an electronic device 100 as described in any of the above embodiments, and the pelvic floor muscle pressure detection device 10 and the electronic device 100 are communicatively connected. The electronic device 100 is used to receive the pelvic floor muscle pressure value of the object being measured transmitted by the pelvic floor muscle pressure detection device 10, and generate a pelvic floor muscle pressure distribution view based on the pelvic floor muscle pressure value of the object being measured.

[0091] In this embodiment, the electronic device 100 includes one or more processors; a memory, in which one or more programs are stored, wherein when the one or more programs are executed by one or more processors, the one or more processors execute the steps in the above-mentioned method embodiments.

[0092] In one embodiment, Fig.10, which shows a schematic diagram of the structure of an electronic device 100 for receiving the pelvic floor muscle pressure value of the object under test transmitted by the pelvic floor muscle pressure detection device 10. The electronic device 100 includes a central processing unit (CPU) 101, which can perform various appropriate actions and processes according to the program stored in the read-only memory (ROM) 102 or the program loaded from the storage part 108 to the random access memory (RAM) 103. In the RAM 103, various programs and data required for the operation of the electronic device 100 are also stored. The CPU 101, the ROM 102, and the RAM 103 are connected to each other through the bus 104. The input / output (I / O) interface 105 is also connected to the bus 104.

[0093] The following components are connected to the I / O interface 105: an input section 106 including a keyboard, a mouse, etc.; an output section 107 including a cathode ray tube (CRT), a liquid crystal display (LCD), etc., and a speaker, etc.; a storage section 108 including a hard disk, etc.; and a communication section 109 including a network interface card such as a LAN card, a modem, etc. The communication section 109 performs communication processing via a network such as the Internet. A drive 110 is also connected to the I / O interface 105 as needed. A removable medium 111, such as a magnetic disk, an optical disk, a magneto-optical disk, a semiconductor memory, etc., is installed on the drive 110 as needed, so that a computer program read therefrom is installed into the storage section 108 as needed.

[0094] In this embodiment, refer to Fig. 9 The pelvic floor muscle pressure detection device 10 transmits the calculated pelvic floor muscle pressure value to the electronic device 100 via the USB data cable 3. The software platform on the electronic device 100 receives and parses the pelvic floor muscle pressure value data. As a feasible implementation method for generating a pelvic floor muscle pressure distribution view, the software platform maps each pressure value to a corresponding two-dimensional or three-dimensional coordinate system based on the layout information of the ion-type pressure sensor array 12. Based on the mapped data, the software platform generates a pelvic floor muscle pressure distribution view. Fig.11 The pelvic floor muscle pressure distribution view can use color coding to indicate the pressure in different areas, forming an intuitive visual presentation of the pelvic floor muscle pressure distribution. Through the above implementation, it is possible to generate a pelvic floor muscle pressure distribution view based on the pelvic floor muscle pressure value of the measured object, providing intuitive auxiliary information for clinical diagnosis and treatment.

[0095] In summary, the pelvic floor muscle pressure detection device and system of the present embodiment, on the one hand, can better fit the pelvic floor muscle of the object to be measured through the probe structure including the flexible shell 11 and the ion-type pressure sensor array 12, ensure the close contact and detection point coverage of the sensor array and the pelvic floor muscle, and reduce the detection error caused by poor contact or incomplete detection area. Since the ion-type pressure sensor array 12 has the characteristics of high sensitivity and rapid response, it can accurately capture the pressure changes of each detection point of the pelvic floor muscle, further improving the accuracy of the detection result. On the other hand, the signal processing module 21 works under the action of the positive excitation voltage and the negative excitation voltage based on the capacitance value of the reference capacitor. First, by alternately applying the positive excitation voltage and the negative excitation voltage, the nonlinear error and parasitic capacitance interference of the ion-type pressure sensor array 12 can be eliminated, further improving the accuracy of pelvic floor muscle pressure detection, and meeting the needs of high-precision pressure distribution measurement of the pelvic floor muscle. Secondly, by adjusting the capacitance value of the reference capacitor (Cr1-Crn), the signal processing module 21 can be optimized according to different detection requirements, especially in the micro-pressure range, to provide higher sensitivity and better adaptability. At the same time, the device of the present application has a simple mechanical structure, which not only improves the accuracy of pelvic floor muscle detection, but also reduces the manufacturing cost, so that the pelvic floor muscle pressure detection device 10 has significant economic benefits whether it is used in medical clinics or in personal home medical terminals to provide convenient pelvic floor muscle pressure detection.

[0096] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present application, rather than to limit it. Although the present application has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or replace some or all of the technical features therein with equivalents. However, these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present application.

[0097] In addition, those skilled in the art will appreciate that, although some embodiments herein include certain features included in other embodiments but not other features, the combination of features of different embodiments is meant to be within the scope of the present application and form different embodiments. For example, in the above claims, any one of the claimed embodiments may be used in any combination. The information disclosed in this background technology section is intended only to deepen the understanding of the overall background technology of the present application and should not be regarded as an admission or in any form of implication that the information constitutes prior art known to those skilled in the art.

Claims

1. A pelvic floor muscle pressure detection device, characterized in that: The device comprises: A probe, the probe comprising a flexible housing and an ion-type pressure sensor array, the ion-type pressure sensor array being arranged on the inner surface of the flexible housing in the form of an array of m rows and n columns, for detecting the pelvic floor muscle pressure of the subject being measured when the probe is inserted into the cavity of the subject being measured, and converting the pelvic floor muscle pressure into a sensing capacitance signal, m and n being integers greater than or equal to 1; the flexible housing comprising a tubular portion and a spherical portion located at the top of the tubular portion, the ion-type pressure sensor array being arranged on the inner surfaces of the tubular portion and the spherical portion respectively; A handle, wherein the handle is connected to the probe, and the handle is provided with a signal processing module, wherein the signal processing module is electrically connected to the ion-type pressure sensor array, and the signal processing module is used to convert the sensing capacitance signal generated by the ion-type pressure sensor array into a detection voltage signal under the action of a positive excitation voltage and a negative excitation voltage based on adjusting the capacitance value of a reference capacitor, and obtain the pelvic floor muscle pressure value of the object under test based on the detection voltage signal, wherein the capacitance value of the reference capacitor is configured to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than a first threshold.

2. The pelvic floor muscle pressure detection device according to claim 1, characterized in that: The ion-type pressure sensor array is evenly spaced and arranged on the inner surface of the flexible housing in the form of an array of m rows and n columns.

3. The pelvic floor muscle pressure detection device according to claim 1, characterized in that: The ion-type pressure sensor array is arranged in an array form of m rows and n columns at uneven intervals on the inner surface of the flexible shell, wherein the arrangement density of the ion-type pressure sensor array in a first length region where the probe is close to the handle is greater than the arrangement density in a second length region where the probe is far from the handle.

4. The pelvic floor muscle pressure detection device according to claim 2 or 3, characterized in that: The signal processing module includes a control unit and at least one capacity-voltage conversion circuit; The capacitance-to-pressure conversion circuit comprises an operational amplifier and the reference capacitor, wherein two ends of the reference capacitor are respectively connected to an inverting input terminal and an output terminal of the operational amplifier, wherein the inverting input terminal of the operational amplifier is configured to be connected to a detection terminal of an ion-type pressure sensor of a corresponding column in the ion-type pressure sensor array; the non-inverting input terminal of the operational amplifier is configured to alternately input the positive excitation voltage and the negative excitation voltage, and the output terminal of the operational amplifier is configured to output a first detection voltage and a second detection voltage corresponding to the positive excitation voltage and the negative excitation voltage, respectively, when a reference voltage is input to a driving terminal of an ion-type pressure sensor of a target row in the ion-type pressure sensor array; The control unit is connected to the output end of the operational amplifier, and is used to calculate the capacitance value of the ion-type pressure sensor in the target row in the ion-type pressure sensor array based on the amplitudes of the positive excitation voltage and the negative excitation voltage, the first detection voltage and the second detection voltage, and the capacitance value of the reference capacitor, and convert the capacitance value of the ion-type pressure sensor in the target row into the pelvic floor muscle pressure value of the object being measured.

5. The pelvic floor muscle pressure detection device according to claim 4, characterized in that: The signal processing module includes a first multiplexer selection unit and a second multiplexer selection unit, wherein the first multiplexer selection unit is used to input a reference voltage to a driving end of the off-line pressure sensor of the target row; The second multiplexer is used to sequentially connect the detection ends of at least one column of the ion-type pressure sensors in the ion-type pressure sensor array to the inverting input end of at least one operational amplifier.

6. The pelvic floor muscle pressure detection device according to claim 1, characterized in that: The reference capacitor comprises a reference capacitor group including a plurality of sub-reference capacitors connected in parallel, and each of the plurality of sub-reference capacitors is connected in series with a switch; The capacitance value of the reference capacitor is configured to be adjusted downward to adapt to the detection of pelvic floor muscle pressure less than a first threshold, including: controlling the switch connected in series with at least one sub-reference capacitor connected in parallel in the reference capacitor group to be disconnected, thereby reducing the capacitance value of the reference capacitor group.

7. The pelvic floor muscle pressure detection device according to claim 1, characterized in that: The probe is connected to the handle in a snap-fit ​​manner. When the probe is connected to the handle, the ion-type pressure sensor array is triggered to be electrically connected to the signal processing module.

8. The pelvic floor muscle pressure detection device according to claim 7, characterized in that: The handle further comprises a probe release button assembly, and the probe release button assembly is used for separating the probe from the handle by pressing when the probe is connected to the handle.

9. The pelvic floor muscle pressure detection device according to claim 1, characterized in that: The handle also includes an indicator light and a USB data cable. The indicator light is arranged on the outer side wall of the handle and is electrically connected to the signal processing module to indicate the pelvic floor muscle detection status; the USB data cable is electrically connected to the signal processing module to power the signal processing module and transmit the pelvic floor muscle pressure value of the subject to be measured to the electronic device.

10. A pelvic floor muscle pressure detection system, characterized in that: The pelvic floor muscle pressure detection system includes a pelvic floor muscle pressure detection device as described in any one of claims 1 to 9 and an electronic device, the pelvic floor muscle pressure detection device and the electronic device are communicatively connected, the electronic device is used to receive the pelvic floor muscle pressure value of the object under test transmitted by the pelvic floor muscle pressure detection device, and generate a pelvic floor muscle pressure distribution view based on the pelvic floor muscle pressure value of the object under test.

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