Method and device for measuring intermuscular pressure based on shear wave mechanical imaging

Abstract

The application relates to an intermuscular pressure measurement method and device based on shear wave mechanical imaging, wherein the method comprises the following steps: establishing a constitutive equation of active dynamics behavior, and determining a stress-strain relationship, a shear wave group velocity function and an intermuscular pressure function of a muscle group; based on the constitutive equation, measuring an elastic modulus of the muscle group in an initial state, a first shear wave group velocity or a first phase velocity of a subject in an external pressure-free state in a target posture, and a second shear wave group velocity or a second phase velocity of the subject in an external pressure state in the target posture; determining a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship, and obtaining intermuscular pressure change information in different states in combination with the second shear wave group velocity or the second phase velocity. Therefore, the problems that the prior art is difficult to simultaneously realize non-destructive in-vivo mechanical characterization of specific muscles, continuous monitoring of changes in in-vivo intermuscular pressure and intermuscular pressure monitoring in multiple regions are solved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of intermuscular pressure measurement, in particular to an intermuscular pressure measurement method and device based on shear wave mechanical imaging. BACKGROUND

[0002] Because the skeletal muscle contains a large amount of water, it can be described as a two-phase material, and more and more studies show that the intermuscular pressure (the hydrostatic pressure in the muscle, IMP) can effectively reflect the physiological state and functional characteristics of the skeletal muscle, and is closely related to many muscle diseases, such as acute and chronic compartment syndrome, muscle injection pain, tendinopathy, etc.

[0003] When the intermuscular pressure is too high, it will cause the blood circulation in the muscle to be blocked, resulting in acute ischemic injury of the muscle and nerve and related inflammatory reactions. Accurate evaluation of the intermuscular pressure of the skeletal muscle helps to make a complete mechanical modeling of the muscle, so as to describe the current physiological state of the muscle and the response when the muscle is actively or passively contracted; based on the comparison of the intermuscular pressures of the bilateral muscles and the comparison of the intermuscular pressures among people, the degree of muscle injury, the degree of fatigue, and the symmetry can be quantitatively evaluated, and the diagnosis of muscle injection pain and intermuscular pressure related diseases can also be helped, thereby playing an important role in the fields of sports health, sports rehabilitation, clinical diagnosis, etc.

[0004] Elastography is a general term for a class of methods for measuring the mechanical properties of tissues in vivo, and a typical elastography method includes four steps:

[0005] 1. Apply mechanical excitation to the tissue to cause deformation or vibration of the soft tissue;

[0006] 2. Use ultrasonic imaging, sensor acquisition, etc. to record the response of the soft tissue to the mechanical excitation, such as the deformation field of the tissue, the vibration field of the particle, wave propagation, etc.;

[0007] 3. Put the mechanical excitation signal and the acquired response into a mechanical model matched with the mechanical behavior of the tissue to quantitatively invert the mechanical properties of the tissue;

[0008] 4. Correlate the mechanical parameters of the tissue with diseases, etc. to further explore the clinical application of elastography.

[0009] Typical mechanical parameters measured by elastography include elastic modulus (directly related to hardness, the most important result presented by elastography), viscoelastic parameters (reflecting tissue viscosity, related to fatty liver, etc.), hyperelastic parameters (reflecting the strain hardening behavior of the tissue), etc. By giving a constitutive relation (a mathematical model reflecting the relationship between tissue deformation and stress), the stress level of the tissue can also be indirectly measured; in recent years, with the continuous deepening of the study of tissue biomechanics and the progress of various in vivo tissue mechanical response collection methods (such as imaging and sensor technology), elastography methods have been continuously developed. In terms of intermuscular pressure detection, the existing technologies on the clinical and scientific research sides are as follows:

[0010] 1. Light-catheter technology (as shown in (a) in Figure 1 ): The design principle of light-catheter is to maintain the patency of the catheter by placing a small fiber or filament at the tip of the catheter; due to the scarcity of fluid content in many tissues, the study of tissue fluid pressure is highly dependent on the optimal contact between the free fluid in the tissue and the physiological saline in the measuring device.

[0011] The light-catheter fiber ensures the continuity of the fluid and significantly increases the contact area between the physiological saline and the catheter filling area; since there is no fluid-gas interface inside or around the light-catheter fiber, capillary phenomenon is avoided, allowing immediate recording of tissue fluid pressure. Under normal circumstances, there is no osmosis between tissue fluid and the light-catheter boundary, and even red blood cells can freely pass between the light-catheter fibers; solutes and particles larger than 1 micrometer in diameter can be considered osmotically inert in this context. The measurement accuracy of the light-catheter is affected by the material of the light-catheter fiber (such as cotton, silk, nylon, polyester, etc.) and the degree of tightness of the wrapping, so the light-catheter must be thoroughly cleaned and disinfected before each measurement.

[0012] 2. Slit catheter technology (as shown in (b) in Figure 1 ): Slit catheter technology is based on a similar principle to light-catheter, with a specially designed catheter tip containing 5 plastic petal structures 30 mm long, which can maintain the patency of the catheter without infusing physiological saline. The significant advantage of this system is that it is more sensitive to changes in tissue fluid pressure, especially in the study of dynamic physiological processes such as muscle contraction; the more open design of the catheter tip not only effectively extends the service life of the catheter, but also allows the removal of possible blood clots in the body by simple finger pressure; however, slit catheter technology also has limitations. Compared with catheters containing light-catheter fibers, these open catheters are more prone to air bubbles during operation, which can adversely affect measurement accuracy. Therefore, special attention should be paid to the generation of air bubbles and their potential impact on measurement results when using slit catheters to measure tissue fluid pressure.

[0013] 3. Myopress catheter (as shown in (c) of Figure 1 Myopress catheter system monitors the fluid pressure in real time through the holes on the side of the catheter, which exhibits a very high dynamic response even at an infusion rate of 0.2 mL / h or lower; this technology is known for its ease of operation and relatively low cost; however, it is worth noting that due to the presence of inertial pressure artifacts, this method limits the types of movements that subjects or patients can perform in application, which needs to be noted and regulated when used.

[0014] 4. Optical fiber catheter is a sensor tip catheter, which is characterized by its immunity to fluid artifacts when measuring intermuscular pressure. In terms of dynamic response, the optical fiber catheter system is comparable to the Myopress system,

[0015] both of which can provide highly sensitive real-time monitoring. However, the optical fiber catheter itself is relatively large and must be embedded inside a catheter filled with saline; compared with other small catheter systems, this larger sheath design may cause relative discomfort to the subject or patient; in addition, the large volume of the optical fiber system may also cause a piston effect during movement, i.e., positive and negative IMP artifacts generated when the catheter moves, which may affect the accuracy of the measurement results; more seriously, in the case of intense or abnormal movement, the optical fiber itself is at risk of breaking, which may cause measurement interruption or data loss; therefore, when using the optical fiber catheter system, special attention needs to be paid to patient comfort, movement status, and fiber durability, etc.

[0016] 5. Electronic sensor catheter (as shown in (d) of Figure 1 The electronic sensor catheter exhibits significant advantages in monitoring intermuscular pressure changes due to its excellent dynamic response performance and immunity to physiological saline columns; however, when the catheter is initially inserted into the skeletal muscle, no fluid is usually present in the tissue space, which may result in the observation of negative intermuscular pressure due to the piston effect; in addition, as the catheter is inserted and the muscle is experimentally contracted, edema fluid or blood bags are often formed, which may in turn cause local fluctuations in intermuscular pressure during movement. Therefore, when using the electronic sensor catheter to monitor intermuscular pressure, these potential influencing factors need to be fully considered.

[0017] In summary, with the development of muscle biomechanics research and the progress of corresponding instruments and equipment, a series of new methods for in vivo characterization of intermuscular pressure have been developed. However, the existing technology is difficult to simultaneously achieve non-invasive in vivo biomechanical characterization of specific muscles, continuous monitoring of changes in in vivo intermuscular pressure, and intermuscular pressure monitoring in multiple regions, which needs to be solved urgently. SUMMARY

[0018] The application provides an intermuscular pressure measurement method and device based on shear wave mechanical imaging, to solve the problem that the prior art cannot simultaneously realize non-destructive in-vivo mechanical characterization of a specific muscle, continuous monitoring of changes in in-vivo intermuscular pressure, and intermuscular pressure monitoring in multiple regions.

[0019] The first aspect of the application provides an intermuscular pressure measurement method based on shear wave mechanical imaging, comprising the following steps: establishing a constitutive equation of active mechanical behavior corresponding to a target muscle group of a target subject, and determining a stress-strain relationship, a shear wave group velocity function, and an intermuscular pressure function of the target muscle group according to the constitutive equation; based on the constitutive equation, measuring the elastic modulus of the target muscle group in a preset initial state, the first shear wave group velocity or the first phase velocity of the target subject in an external pressure-free state in a target posture, and the second shear wave group velocity or the second phase velocity of the target subject in an external pressure state in the target posture; based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, determining a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship, to obtain intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

[0020] Optionally, in one embodiment of the application, before establishing the constitutive equation of the active mechanical behavior corresponding to the target muscle group of the target subject, the method further comprises: applying a target internal pressure or a target external pressure to the target muscle group through a preset pressure strategy, so that the target muscle group performs corresponding movement operations according to the preset trajectory.

[0021] Optionally, in one embodiment of the application, after obtaining the intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity, the method further comprises: constructing an intermuscular pressure change curve of the target muscle group according to the intermuscular pressure change information of the target muscle group in different states; analyzing the intermuscular pressure change curve to obtain an analysis result of the intermuscular pressure change curve, and evaluating the mechanical function and health status of the target muscle group according to the analysis result.

[0022] Optionally, in an embodiment of the present application, the obtaining the intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity comprises: substituting the second shear wave group velocity or the second phase velocity into the shear wave velocity-intermuscular pressure relationship to obtain an active force level of the target muscle group in different states; and determining the intermuscular pressure of the target muscle group in each state according to the active force level to obtain the intermuscular pressure change information of the target muscle group in different states through the intermuscular pressure in each state.

[0023] In a second aspect, an embodiment of the present application provides a device for measuring intermuscular pressure based on shear wave mechanical imaging, comprising: a establishing module configured to establish a constitutive equation of active mechanical behavior of a target muscle group of a target subject, and determine a stress-strain relationship, a shear wave group velocity function and an intermuscular pressure function of the target muscle group according to the constitutive equation; a measuring module configured to measure an elastic modulus of the target muscle group in a preset initial state, a first shear wave group velocity or a first phase velocity of the target subject in an external pressure-free state in a target posture, and a second shear wave group velocity or a second phase velocity of the target subject in an external pressure state in the target posture based on the constitutive equation; and a determining module configured to determine a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, so as to obtain intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

[0024] Optionally, in an embodiment of the present application, the device further comprises an executing module configured to apply a target internal pressure or a target external pressure to the target muscle group through a preset pressure strategy before the establishing module establishes the constitutive equation of the active mechanical behavior of the target muscle group of the target subject, so that the target muscle group performs corresponding movement operations according to the preset trajectory.

[0025] Optionally, in an embodiment of the present application, the device further comprises a constructing module configured to construct an intermuscular pressure change curve of the target muscle group according to the intermuscular pressure change information of the target muscle group in different states after the determining module obtains the intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity; and an analyzing module configured to analyze the intermuscular pressure change curve to obtain an analysis result of the intermuscular pressure change curve, and evaluate a mechanical function and a health condition of the target muscle group according to the analysis result.

[0026] Optionally, in an embodiment of the present application, the determining module comprises: a substituting unit configured to substitute the second shear wave group velocity or the second phase velocity into the shear wave velocity-muscle interstitial pressure relationship formula to obtain an active force level of the target muscle group in different states; and a generating unit configured to determine the muscle interstitial pressure of the target muscle group in each state according to the active force level, so as to obtain muscle interstitial pressure change information in different states through the muscle interstitial pressure in each state.

[0027] In a third aspect, an electronic device is provided, which comprises a memory, a processor, and a computer program stored in the memory and executable on the processor, and the processor executes the program to implement the method for measuring muscle interstitial pressure based on shear wave mechanical imaging according to the above embodiments.

[0028] In a fourth aspect, a computer readable storage medium is provided, which stores a computer program executable by a processor to implement the method for measuring muscle interstitial pressure based on shear wave mechanical imaging according to the above embodiments.

[0029] In a fifth aspect, a computer program product is provided, which comprises a computer program executable to implement the method for measuring muscle interstitial pressure based on shear wave mechanical imaging according to the above embodiments.

[0030] Therefore, the embodiments of the present application have the following beneficial effects:

[0031] The embodiments of the present application can establish a constitutive equation of active mechanical behavior corresponding to a target muscle group of a target subject, and determine a stress-strain relationship, a shear wave group velocity function, and a muscle interstitial pressure function of the target muscle group according to the constitutive equation; measure an elastic modulus of the target muscle group in a preset initial state, a first shear wave group velocity or a first phase velocity when the target subject is in an external pressure-free state in a target posture, and a second shear wave group velocity or a second phase velocity when the target subject is in an external pressure state in the target posture based on the constitutive equation; determine a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-muscle interstitial pressure relationship formula based on the shear wave group velocity function, the muscle interstitial pressure function, the first shear wave group velocity or the first phase velocity, so as to obtain muscle interstitial pressure change information of the target muscle group in different states according to the shear wave velocity-muscle interstitial pressure relationship formula and the second shear wave group velocity or the second phase velocity, thereby enabling real-time, rapid, and convenient in-vivo mechanical characterization of muscle interstitial pressure. Thus, the problems that the prior art is difficult to simultaneously achieve non-invasive in-vivo mechanical characterization of specific muscles, continuous monitoring of changes in in-vivo muscle interstitial pressure, and multiple regional monitoring of muscle interstitial pressure are solved.

[0032] Additional aspects and advantages of the application will be set forth in part in the description which follows, and in part will become apparent to those skilled in the art upon examination of the following and the attached drawings. BRIEF DESCRIPTION OF DRAWINGS

[0033] The above and / or additional aspects and advantages of the present application will become apparent and be readily appreciated from the following description, including the appended drawings.

[0034] Figure 1 (a) in FIG. 1 is a schematic diagram of a lampwick catheter provided in an embodiment of the present application;

[0035] Figure 1 (b) in FIG. 1 is a schematic diagram of a slit catheter provided in an embodiment of the present application;

[0036] Figure 1 (c) in FIG. 1 is a schematic diagram of a Myopress catheter provided in an embodiment of the present application;

[0037] Figure 1 (d) in FIG. 1 is a schematic diagram of an electronic sensor catheter provided in an embodiment of the present application;

[0038] Figure 2 FIG. 2 is a flowchart of a method for measuring intermuscular pressure based on shear wave mechanical imaging according to an embodiment of the present application;

[0039] Figure 3 (a) in FIG. 3 is a schematic diagram of passive muscle SWV change with IMP provided in an embodiment of the present application;

[0040] Figure 3 (b) in FIG. 3 is a schematic diagram of IMP effect on SWV under different active parameters provided in an embodiment of the present application;

[0041] Figure 3 (c) in FIG. 3 is a schematic diagram of the effect of hyperelasticity parameter α change in a wide range on the relationship between SWV and IMP provided in an embodiment of the present application;

[0042] Figure 3 (d) in FIG. 3 is a schematic diagram of the effect of hyperelasticity parameter β change in a wide range on the relationship between SWV and IMP provided in an embodiment of the present application;

[0043] Figure 4 (a) in FIG. 4 is a schematic diagram of an experiment using a syringe to pressurize in a porcine skeletal muscle ex vivo experiment provided in an embodiment of the present application;

[0044] Figure 4(b) is an experimental measurement result and reverse result schematic diagram of intermuscular pressure in a pig skeletal muscle in vitro experiment process provided by an embodiment of the present application;

[0045] Figure 4 (c) is a SWV (1.64 m / s) schematic diagram of a pig skeletal muscle under 0 mmHg in a pig skeletal muscle in vitro experiment process provided by an embodiment of the present application;

[0046] Figure 4 (d) is a SWV (3.52 m / s) schematic diagram of a pig skeletal muscle under 100 mmHg in a pig skeletal muscle in vitro experiment process provided by an embodiment of the present application;

[0047] Figure 5 (a) is an experimental schematic diagram of an IMP in a body inversion experiment using cuff pressure provided by an embodiment of the present application;

[0048] Figure 5 (b) is an in vivo inversion result schematic diagram of an IMP provided by an embodiment of the present application;

[0049] Figure 5 (c) is an in vivo experiment schematic diagram provided by an embodiment of the present application;

[0050] Figure 6 is an example diagram of an intermuscular pressure measuring device based on shear wave mechanical imaging according to an embodiment of the present application;

[0051] Figure 7 is a structural schematic diagram of an electronic device provided by an embodiment of the present application.

[0052] Wherein, 10 is an intermuscular pressure measuring device based on shear wave mechanical imaging; 100 is a establishing module, 200 is a measuring module, 300 is a determining module; 701 is a memory, 702 is a processor, 703 is a communication interface. DETAILED DESCRIPTION

[0053] The embodiments of the present application are described in detail below, examples of which are shown in the accompanying drawings, wherein the same or similar notations represent the same or similar elements or elements having the same or similar functions throughout. The embodiments described below by referring to the accompanying drawings are exemplary and are intended to explain the present application, and cannot be understood as a limitation of the present application.

[0054] With reference to the accompanying drawings, the method and device for measuring intermuscular pressure based on shear wave mechanical imaging according to embodiments of the present application are described below. In view of the problems mentioned in the background, the present application provides a method for measuring intermuscular pressure based on shear wave mechanical imaging. In the method, a constitutive equation of active muscle behavior corresponding to a target muscle group of a target subject is established, and a stress-strain relationship, a shear wave group velocity function and an intermuscular pressure function of the target muscle group are determined according to the constitutive equation. Based on the constitutive equation, the elastic modulus of the target muscle group in a preset initial state, the first shear wave group velocity or the first phase velocity when the target subject is in an external pressure state in a target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in an external pressure state in the target posture are measured. Based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship are determined, so that the intermuscular pressure change information of the target muscle group in different states is obtained according to the shear wave velocity-intermuscular pressure relationship and the second shear wave group velocity or the second phase velocity, thereby enabling real-time, rapid and convenient in-vivo mechanical characterization of intermuscular pressure. Thus, the problems that the prior art is difficult to simultaneously realize non-invasive in-vivo mechanical characterization of specific muscles, continuous monitoring of changes in in-vivo intermuscular pressure, and intermuscular pressure monitoring in multiple regions are solved.

[0055] Specifically, Figure 1 A flowchart of the method for measuring intermuscular pressure based on shear wave mechanical imaging according to an embodiment of the present application is shown in FIG. 1.

[0056] As Figure 1 shown, the method for measuring intermuscular pressure based on shear wave mechanical imaging includes the following steps:

[0057] In step S101, a constitutive equation of active muscle behavior corresponding to a target muscle group of a target subject is established, and a stress-strain relationship, a shear wave group velocity function and an intermuscular pressure function of the target muscle group are determined according to the constitutive equation.

[0058] According to the embodiments of the present application,

[0059] 1. Select a constitutive equation suitable for describing the active muscle behavior. The constitutive equation contains at least the following basic variables:

[0060] (a) Initial elastic modulus μ0, used to describe the elastic modulus of the muscle in the initial state;

[0061] (b) Active force level σ0, used to describe the level of active muscle force, so as to study the intermuscular pressure when the active force is applied.

[0062] The constitutive equation will determine the stress-strain relationship of the muscle:

[0063] σp = f p (μ0, ω a , λ,...)(1)

[0064] σ0= f0(μ0, ω a , λ,...)(2)

[0065] and the shear wave group velocity function and the intermuscular pressure function of the muscle:

[0066] c = f c (μ0, ω a , λ,...)(3)

[0067] p = f a (μ0, ω a , λ,...)(4)

[0068] wherein λ is the elongation ratio (which can be converted into strain) of the muscle compared to the initial state of the muscle, μ0in the above two parameters is necessary, the active parameter ω a is introduced to be able to more accurately depict the active dynamics behavior of the muscle, thereby inverting the intermuscular pressure change under the active force state, but is not necessary.

[0069] It should be noted that the embodiments of the present application are also applicable to the inversion of the intermuscular pressure under the passive constitutive relation, in addition to which other parameters need to be added on the basis of the two parameters. In addition, in the actual execution process, the person skilled in the art can also take some deformation of the above two parameters (such as taking E0= f0= 3μ0as a kind of alternative of the initial elastic modulus) as the basic variable, which is not limited here.

[0070] Therefore, the embodiments of the present application select the constitutive equation suitable for describing the active dynamics behavior of the muscle, thereby providing reliable theory and data support for subsequent measurement of the intermuscular pressure of the specific muscle of the human body under a specific state.

[0071] Optionally, in an embodiment of the present application, before the constitutive equation corresponding to the active dynamics behavior of the target muscle group of the target subject is established, it further comprises: applying a target internal pressure or a target external pressure to the target muscle group through a preset pressure strategy, so that the target muscle group performs corresponding movement operation according to the preset trajectory.

[0072] It should be noted that before the constitutive equation corresponding to the active dynamics behavior of the target muscle group of the target subject is established, the embodiments of the present application also need to inject or externally press the specific muscle part of the subject through a cuff or a syringe, so that the muscle group such as skeletal muscle bears a quantitative internal or external pressure, and then the specific muscle group moves according to the predetermined trajectory, such as keeping the elbow joint at a 90-degree angle.

[0073] Thus, the embodiments of the present application ensure effective measurement of the change of the intermuscular pressure in the sequence by making the specified muscles move in the specified sequence.

[0074] In step S102, based on the constitutive equation, the elastic modulus of the target muscle group in the preset initial state, the first shear wave group velocity or the first phase velocity of the target subject in the target posture when the target subject is in the state without external pressure, and the second shear wave group velocity or the second phase velocity of the target subject in the target posture when the target subject is in the state with external pressure are measured.

[0075] In step S103, based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, the plurality of undetermined parameters of the constitutive equation and the shear wave velocity-intermuscular pressure relationship are determined to obtain the intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

[0076] After the constitutive equation is determined, further, the embodiments of the present application first need to measure the elastic modulus μ0 of the muscle in the initial state by one or more combinations of methods such as the muscle hardness meter, static elastography, shear wave elastography and the like; wherein the initial state is defined as the state in which the muscle has no active force and no external pressure, and the initial state should in principle be selected as the state in which the muscle is passively stretched the least.

[0077] Secondly, the embodiments of the present application measure the shear wave group velocity or phase velocity (i.e. the first shear wave group velocity or the first phase velocity) c0 of the muscle in the target posture when the subject is in the target posture and has no external pressure.

[0078] Thirdly, the embodiments of the present application can measure the shear wave group velocity or phase velocity (i.e. the second shear wave group velocity or the second phase velocity) c p .

[0079] Then, the measured c0 is substituted into the formula (3) and the formula (4) to obtain all the undetermined parameters including ω a in the constitutive equation of the muscle and the relationship between the shear wave velocity and the intermuscular pressure.

[0080] Optionally, in an embodiment of the present application, the intermuscular pressure change information of the target muscle group in different states is obtained according to the shear wave speed-muscle interstitial pressure relationship, the second shear wave group velocity or the second phase velocity, including: substituting the second shear wave group velocity or the second phase velocity into the shear wave speed-muscle interstitial pressure relationship to obtain the active force level of the target muscle group in different states; determining the muscle interstitial pressure of the target muscle group in each state according to the active force level, so as to obtain the intermuscular pressure change information in different states through the muscle interstitial pressure in each state.

[0081] In the process of implementation, the embodiment of the present application also needs to substitute c p into the above relationship between shear wave speed and muscle interstitial pressure to obtain the muscle interstitial pressure in the current state, and to give the active parameters ω a of different states to obtain the muscle interstitial pressure in each state, so that the change of the muscle interstitial pressure in the sequence can be obtained during the change of the muscle physiological state.

[0082] Therefore, the embodiment of the present application can separately perform in vivo mechanical characterization on specific muscles, and can non-invasively and quantitatively measure the muscle interstitial pressure.

[0083] Optionally, in an embodiment of the present application, after obtaining the intermuscular pressure change information of the target muscle group in different states according to the shear wave speed-muscle interstitial pressure relationship, the second shear wave group velocity or the second phase velocity, it further includes: constructing the intermuscular pressure change curve of the target muscle group according to the intermuscular pressure change information of the target muscle group in different states; analyzing the intermuscular pressure change curve to obtain the analysis result of the intermuscular pressure change curve, and evaluating the mechanical function and health status of the target muscle group according to the analysis result.

[0084] It should be noted that after obtaining the intermuscular pressure change information of the target muscle group in different states, the embodiment of the present application evaluates the mechanical function and health status of the muscle by analyzing the change curve of the muscle interstitial pressure in the sequence, and displays the change curve of the muscle interstitial pressure in the specified sequence or the further analysis result (such as extreme value) of the curve through an electronic display screen, a printer, etc., so that the change of the in vivo intermuscular pressure can be monitored in real time.

[0085] In addition, the present application can also construct a shear wave mechanical imaging-based intermuscular pressure measurement system according to the above shear wave mechanical imaging-based intermuscular pressure measurement method, and the execution logic of the shear wave mechanical imaging-based intermuscular pressure measurement system is introduced and described below.

[0086] The shear wave mechanical imaging-based intermuscular pressure measurement system of the present application mainly includes a muscle pressure applying module, a muscle movement constraint module, a muscle shear wave excitation module, a muscle shear wave acquisition module, a muscle interstitial pressure model and inversion module, and a muscle interstitial pressure presentation module.

[0087] Muscle pressure applying module: This module can make certain muscle groups bear a certain load, for example, the skeletal muscle can bear a certain internal or external pressure through a cuff or a syringe, etc.

[0088] Muscle movement constraint module: This module can make certain muscle groups move along a predetermined trajectory, for example, the elbow joint can be kept at a 90-degree angle at all times through a limiting unit or a servo motor, etc.

[0089] Muscle shear wave excitation module: This module can excite shear waves in the muscle, for example, through a motor-driven mechanical structure to realize reciprocating vibration, which is in contact with the skin, thereby exciting shear waves in the muscle; the shear wave excitation module can be realized by a motor or a piezoelectric ceramic or focused ultrasound to generate ultrasonic radiation force;

[0090] Muscle shear wave acquisition module: Acquire the shear waves propagating in the muscle and obtain the group velocity / phase velocity of the shear wave propagation, for example, through high-frame-rate ultrasonic imaging (which can be realized by ultrasonic imaging, magnetic resonance imaging, etc. Imaging method or vibration sensor to collect shear waves propagating in the muscle;

[0091] Intermuscular pressure model and inversion module: After measuring the shear wave phase velocity / group velocity c under different conditions, the intermuscular pressure is fitted through the least square method, etc.

[0092] Intermuscular pressure presentation module: This module can display the change curve of the intermuscular pressure of the muscle in the specified sequence or the further analysis result (such as extreme value) of the curve through an electronic display screen, a printer, etc.

[0093] The execution process of the muscle intermuscular pressure measurement method and system based on shear wave mechanical imaging of the present application is described below through a specific embodiment and in conjunction with the drawings, taking the human biceps muscle as an example.

[0094] First, select a constitutive equation suitable for describing the active mechanical behavior of the muscle, which is the muscle active constitutive model proposed by Ehret in 2011, and the expression of its strain energy function is:

[0095]

[0096] Where μ, α, β represent material parameters. μ is the initial shear modulus, and α and β represent the super-elastic hardening index of muscle fibers. m represents the muscle fiber direction, and the invariant and which are related to the right Cauchy-Green strain tensor C and the fiber structure tensor M=m m, and the expression is:

[0097]

[0098]

[0099] det(C) = 1(6)

[0100] Where, w0, w p These represent the weighting factors related to the isotropic tissue components and muscle fiber components of the muscle, respectively. The main advantage of this constitutive model is that it defines an effective active muscle parameter w. a Once w is determined a This allows us to determine the current activation state of the muscle, and the stress can also be obtained from the constitutive equation (7). i (i = 1 to 5) are the invariants of the right Cauchy-Green tensor C and the structural tensor M, which can be determined by the strain of the muscle.

[0101] Based on the selected constitutive equation, this application can further derive the calculation expression for stress in muscle as follows:

[0102]

[0103] And the shear wave velocity and intermuscular pressure are calculated using the following formula:

[0104]

[0105]

[0106] It is important to note that, under this constitutive model, the relationship between the shear wave velocity and each constitutive parameter is as follows: Figure 3 As shown, where, Figure 3 (a) shows the sensitivity of shear wave velocity to IMP. When IMP varies from 0 to 100 mmHg, the shear wave velocity in the passive state (w a =0) increased by approximately 2.5 times; Figure 3 (b) shows the different active parameters w a The change of SWV with IMP under the value, the shear wave velocity with w a The increase in shear wave velocity due to the increase in muscle active contraction and IMP indicates that both the increase in muscle active contraction and IMP lead to a significant increase in shear wave velocity. Figure 3 (c) and Figure 3 (d) highlights the variation of SWV with IMP under different hyperelastic parameters α and β. This indicates that variations in α and β over a wide range have no significant effect on SWV. This result demonstrates that when inferring IMP from measured shear waves, this application only requires population reference values ​​for α and β to invert intermuscular pressure, thus greatly simplifying the inverse method.

[0107] To verify the related theory of the intermuscular pressure measurement method based on shear wave mechanical imaging of the present application, the present application can carry out in vitro experiments and in vivo experiments on porcine skeletal muscle and human biceps brachii respectively to determine the intermuscular pressure.

[0108] In the in vitro experiment of porcine skeletal muscle, the present application can use porcine skeletal muscle obtained from the leg of a freshly slaughtered animal, and the fresh porcine skeletal muscle is kept in an ice box at 2-4°C, and then transported to the laboratory; after thawing for two hours at room temperature, a large uniform area is selected for the experiment, and a pressure system (Transonic SP200) is used to directly measure the IMP corresponding to each pressure level, which is composed of a pressure catheter and a power amplifier; after completing the initial shear wave velocity measurement of the porcine skeletal muscle, the pressure catheter is soaked in clean water for cleaning, and the pressure value is calibrated after drying; after calibration, the pressure catheter is placed in a 0.8mm diameter needle and inserted about 2cm into the surface of the porcine skeletal muscle, and then the needle is slowly pulled out, as shown in (a) of Figure 4 When the residual stress is completely released, an injector filled with water is inserted about 8mm from the pressure catheter in the muscle, and the injector is slowly and uniformly pushed, while the pressure catheter reading is monitored at 20, 40, 60, 80 and 100mmHg. At each pressure, the Verasonics system is used to excite acoustic radiation force and obtain ultrasound signals; at each pressure, 5 SWV measurements are made along the muscle fibers.

[0109] Figure 4 (b) of Figure 4 (c) and Figure 4 (d) of Figure 3 The analysis of

[0110] To verify the effectiveness of the theory and method of the present application on in vivo skeletal muscle intermuscular pressure inversion, the present application further carries out in vivo experiments on the biceps brachii of a healthy male volunteer (age: 26 years old, height: 169.0cm, weight: 66.6kg). The subject expressed informed consent after being explained in detail about the nature of the study and possible consequences.

[0111] First, the passive parameters of the biceps brachii were measured. The volunteer wore an elbow joint fixing support (Ober, EO-30 type), and the arm was placed on the table in a relaxed state. The elbow joint support was used to adjust the elbow joint flexion angle to 90°. Five shear wave velocity measurements were obtained along the muscle fibers, and the passive parameters a and β were inferred using equation 1.8. The values of a and β can still be set as a = 6.3 and β = 5.2.

[0112] Using the derived passive muscle parameters, the correlation between shear wave velocity and intermuscular pressure can be obtained. Then, the IMP of the biceps brachii was evaluated under different cuff pressures. The biceps brachii was placed on the table in a relaxed position, and the initial SWV was measured. Then, a mercury sphygmomanometer cuff was placed on the upper end of the biceps brachii, as shown in (a) of FIG. 6. The pressure was quickly raised to 40 mmHg of mercury column scale value, maintained for 30 seconds, and the shear wave velocity was measured. Then, the air valve was opened to release the pressure, and the volunteer rested for two minutes. Then, the above steps were repeated to measure the shear wave velocity under cuff pressures of 80 and 120 mmHg. Five shear wave velocities were obtained at each pressure, and the B-mode image was monitored in real time to confirm that there was no obvious muscle movement. According to the measured SWV, the IMP under different cuff pressures was inferred, as shown in (c) of FIG. 6. Figure 5 Figure 5

[0113] In addition, the shear wave velocity of the biceps brachii under different cuff pressures was detected, and the IMP in vivo was inverted using equations (8) and (9). The results are shown in (b) of FIG. 7. It can be seen that the muscle shear wave velocity increases with the increase of the cuff pressure. The in vivo change of IMP caused by cuff pressure is 14.9 mmHg, which indicates that the intermuscular pressure measurement method of the present application not only can measure the passive mechanical parameters of the muscle for the evaluation of the muscle state of the volunteer, but also can conveniently and effectively evaluate the muscle function of the volunteer under different physiological conditions. Figure 5 The following explains the relevant modules of the intermuscular pressure measurement system based on shear wave mechanical imaging used in the present application. The muscle pressure applying module in the above specific embodiment is realized by a syringe in vitro and a cuff pressure in vivo, thereby completing the collection of shear wave velocities under different physiological conditions of the muscle. The muscle movement constraint module is a support for fixing the elbow joint, which can accurately control the elbow flexion angle of the volunteer. The muscle shear wave excitation is realized by acoustic radiation force focusing, and the high frame rate ultrasound image acquisition is realized by the Verosonics rapid imaging system. The intermuscular pressure model and inversion method are mainly realized by equations (8) and (9), and finally the statistical fitting is obtained as

[0114] and Figure 4 Figure 5 ​​​The results show that the specific embodiment realizes in-vivo measurement of intermuscular pressure of the biceps of the human body, thereby realizing functional evaluation of the muscle in various physiological states and disease detection.

[0115] According to the intermuscular pressure measurement method based on shear wave mechanical imaging provided in the embodiments of the present application, a constitutive equation of active mechanical behavior corresponding to a target muscle group of a target subject is established, and a stress-strain relationship, a shear wave group velocity function, and an intermuscular pressure function of the target muscle group are determined according to the constitutive equation; based on the constitutive equation, an elastic modulus of the target muscle group in a preset initial state, a first shear wave group velocity or a first phase velocity when the target subject is in an external pressure-free state in a target posture, and a second shear wave group velocity or a second phase velocity when the target subject is in an external pressure state in the target posture are measured; based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship are determined, so as to obtain intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity, thereby enabling real-time, rapid, and convenient in-vivo mechanical characterization of intermuscular pressure.

[0116] Secondly, the intermuscular pressure measurement device based on shear wave mechanical imaging according to the embodiments of the present application is described with reference to the accompanying drawings.

[0117] Figure 6 is a block schematic diagram of the intermuscular pressure measurement device based on shear wave mechanical imaging according to the embodiments of the present application.

[0118] As Figure 6 shown, the intermuscular pressure measurement device based on shear wave mechanical imaging 10 includes an establishing module 100, a measuring module 200, and a determining module 300.

[0119] The establishing module 100 is configured to establish a constitutive equation of active mechanical behavior corresponding to a target muscle group of a target subject, and determine a stress-strain relationship, a shear wave group velocity function, and an intermuscular pressure function of the target muscle group according to the constitutive equation.

[0120] The measuring module 200 is configured to measure, based on the constitutive equation, an elastic modulus of the target muscle group in a preset initial state, a first shear wave group velocity or a first phase velocity when the target subject is in an external pressure-free state in a target posture, and a second shear wave group velocity or a second phase velocity when the target subject is in an external pressure state in the target posture.

[0121] The determining module 300 is configured to determine a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-interstitial pressure relationship based on the shear wave group velocity function, the interstitial pressure function, the first shear wave group velocity, or the first phase velocity, so as to obtain the interstitial pressure change information of the target muscle group in different states according to the shear wave velocity-interstitial pressure relationship, the second shear wave group velocity, or the second phase velocity.

[0122] Optionally, in an embodiment of the present application, the shear wave mechanical imaging based interstitial pressure measuring device 10 further comprises an executing module configured to apply a target internal pressure or a target external pressure to the target muscle group through a preset pressure strategy before establishing the constitutive equation of the target muscle group corresponding to the target subject.

[0123] Optionally, in an embodiment of the present application, the shear wave mechanical imaging based interstitial pressure measuring device 10 further comprises a constructing module and an analyzing module.

[0124] The constructing module is configured to construct an interstitial pressure change curve of the target muscle group according to the interstitial pressure change information of the target muscle group in different states after obtaining the interstitial pressure change information of the target muscle group in different states according to the shear wave velocity-interstitial pressure relationship, the second shear wave group velocity, or the second phase velocity.

[0125] The analyzing module is configured to analyze the interstitial pressure change curve to obtain an analysis result of the interstitial pressure change curve, and evaluate the mechanical function and health status of the target muscle group according to the analysis result.

[0126] Optionally, in an embodiment of the present application, the determining module 200 comprises a substituting unit and a generating unit.

[0127] The substituting unit is configured to substitute the second shear wave group velocity or the second phase velocity into the shear wave velocity-interstitial pressure relationship to obtain the active force level of the target muscle group in different states.

[0128] The generating unit is configured to determine the interstitial pressure of the target muscle group in each state according to the active force level, so as to obtain the interstitial pressure change information in different states through the interstitial pressure in each state.

[0129] It should be noted that the foregoing explanation and description of the shear wave mechanical imaging based interstitial pressure measuring method also apply to the shear wave mechanical imaging based interstitial pressure measuring device, which will not be described here again.

[0130] The intermuscular pressure measuring device based on shear wave mechanical imaging provided by the embodiment of the present application comprises a establishing module configured to establish a constitutive equation of a target muscle group of a target subject, and determine a stress-strain relationship, a shear wave group velocity function and an intermuscular pressure function of the target muscle group according to the constitutive equation; a measuring module configured to measure an elastic modulus of the target muscle group in a preset initial state, a first shear wave group velocity or a first phase velocity of the target subject in an external pressure-free state in a target posture, and a second shear wave group velocity or a second phase velocity of the target subject in an external pressure state in the target posture based on the constitutive equation; and a determining module configured to determine a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, so as to obtain intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship and the second shear wave group velocity or the second phase velocity, thereby enabling real-time, rapid and convenient in-vivo mechanical characterization of the intermuscular pressure.

[0131] Figure 7 The structural schematic diagram of the electronic device provided by the embodiment of the present application is provided. The electronic device can comprise:

[0132] The memory 701, the processor 702 and the computer program stored in the memory 701 and executable on the processor 702.

[0133] The processor 702 implements the intermuscular pressure measuring method based on shear wave mechanical imaging provided in the above embodiment when executing the program.

[0134] Further, the electronic device further comprises:

[0135] The communication interface 703 is configured to communicate between the memory 701 and the processor 702.

[0136] The memory 701 is configured to store the computer program executable on the processor 702.

[0137] The memory 701 can include a high-speed RAM memory, and can also include a non-volatile memory, for example, at least one disk memory.

[0138] If the memory 701, the processor 702 and the communication interface 703 are implemented independently, the communication interface 703, the memory 701 and the processor 702 can be connected with each other through a bus and complete communication between each other. The bus can be an Industry Standard Architecture (ISA) bus, a Peripheral Component (PCI) bus or an Extended Industry Standard Architecture (EISA) bus, etc. The bus can be divided into an address bus, a data bus, a control bus, etc. For convenience of representation, Figure 7 Only one thick line is used to represent the bus in the figure, but it does not mean that there is only one bus or only one type of bus.

[0139] Optionally, in a specific implementation, if the memory 701, the processor 702 and the communication interface 703 are integrated on a chip, the memory 701, the processor 702 and the communication interface 703 can complete communication between each other through an internal interface.

[0140] The processor 702 can be a Central Processing Unit (CPU), or an Application Specific Integrated Circuit (ASIC), or one or more integrated circuits configured to implement one or more embodiments of the present application.

[0141] The embodiment of the present application further provides a computer readable storage medium, which has a computer program stored thereon, and the program is executed by a processor to implement the method for measuring intermuscular pressure based on shear wave mechanical imaging.

[0142] The embodiment of the present application further provides a computer program product, which includes a computer program, and the computer program is executed to implement the method for measuring intermuscular pressure based on shear wave mechanical imaging.

[0143] In the description of the application, reference to "one embodiment", "some embodiments", "an example", "a specific example", or "some examples" means that a particular feature, structure, material, or characteristic being described is included in at least one embodiment or example of the application. The appearances of the phrase in various places in the specification are not necessarily all referring to the same embodiment or example. Furthermore, the described specific features, structures, materials, or characteristics can be combined in any suitable manner in one or more embodiments or examples. In addition, the usage of "N" means at least two, for example, two, three or the like, unless explicitly stated otherwise.

[0144] Furthermore, the terms "first", "second", or the like, are used merely as a designation of certain elements or features, and do not imply or connote relative importance or a specific order of categorization of the indicated features. Accordingly, features described as "first" or "second" can be explicitly or implicitly included in at least one of the features. In the description of the application, the term "N" means at least two, for example, two, three, etc., unless explicitly stated otherwise.

[0145] Any process or method descriptions or blocks in flow charts or otherwise described herein represent embodiments which can be managed as one or more modules, segments, or portions of code which include one or more executable instructions for implementing specific logic functions or steps, and alternate implementations are possible. In some embodiments, the processes and methods described can be executably encoded on a machine- readable medium in a data signal embodied in an electromagnetic signal, a wireless signal, or a propagated signal.

[0146] The logic and / or steps represented in the flowcharts and / or described herein, for example, can be considered as a sequence of instructions to implement logical functions, and can be embodied in any computer-readable medium for use by an instruction execution system, apparatus, or device, such as a computer-based system, processor- based system, or other system that can fetch the instructions from the instruction execution system, apparatus, or device and execute the instructions. For purposes of this specification, a "computer-readable medium" can be any apparatus that can contain, store, communicate, propagate, or transport the program for use by or in connection with the instruction execution system, apparatus, or device. The computer-readable medium can be a computer- readable storage medium or a computer-readable signal medium. The computer- readable storage medium can be, for example, but not limited to, an electronic, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or any suitable combination of the foregoing. More specific examples (a non-exhaustive list) of the computer-readable storage medium include the following: an electrical connection having one or more wires (electrical connections), a portable computer diskette (a magnetic device), a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or Flash memory), an optical fiber, and a portable compact disc read-only memory (CDROM). In addition, the computer-readable medium can even be paper or another suitable medium upon which the program is printed, as the program can be electronically captured, via, for example, optical scanning of the paper or other medium, then compiled, interpreted, or otherwise processed in a suitable manner, if necessary, and then stored in a computer memory.

[0147] It should be understood that aspects of the application can be implemented in hardware, software, firmware or combinations thereof. In the above embodiments, the N steps or methods can be implemented in software or firmware stored in a memory and executed by a suitable instruction execution system. If implemented in hardware and in another embodiment, any of the following technologies, known in the art, or their combinations can be used: discrete logic circuitry having logic gates for implementing logic functions on data signals, application specific integrated circuits having appropriate combinational logic gates, programmable gate arrays (PGA), field programmable gate arrays (FPGA), etc.

[0148] Those skilled in the art can understand that all or part of the steps carried out by the above-mentioned embodiment methods can be completed by programs instructing related hardware, and the programs can be stored in a computer-readable storage medium. When the programs are executed, one or a combination of the steps of the method embodiments is included.

[0149] In addition, each of the functional units in the various embodiments of the present application can be integrated in one processing module, or each of the units can be physically present separately, or two or more units can be integrated in one module. The integrated module can be implemented in the form of hardware or in the form of a software functional module. When the integrated module is implemented in the form of a software functional module and sold or used as an independent product, it can also be stored in a computer readable storage medium.

[0150] The storage medium mentioned above can be a read-only memory, a magnetic disk or an optical disk, etc. Although the embodiments of the present application have been shown and described above, it should be understood that the above embodiments are exemplary and should not be construed as limiting the present application, and those skilled in the art can make changes, modifications, replacements and variations to the above embodiments within the scope of the present application.

Claims

1. An intermuscular pressure measurement method based on shear wave mechanical imaging, characterized in that, The method comprises the following steps. establishing a constitutive equation of active mechanical behavior corresponding to a target muscle group of a target subject, and determining a stress-strain relationship, a shear wave group velocity function and an intermuscular pressure function of the target muscle group according to the constitutive equation; measuring, based on the constitutive equation, an elastic modulus of the target muscle group in a preset initial state, a first shear wave group velocity or a first phase velocity of the target subject in a target posture when the target subject is in an external pressure-free state, and a second shear wave group velocity or a second phase velocity of the target subject in the target posture when the target subject is in an external pressure state; determining, based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship, so as to obtain intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

2. The method of claim 1, wherein, Before establishing the constitutive equation of the active mechanical behavior corresponding to the target muscle group of the target subject, the method further comprises: applying a target internal pressure or a target external pressure to the target muscle group through a preset pressure strategy, so that the target muscle group performs corresponding movement operation according to a preset trajectory.

3. The method of claim 1, wherein, After obtaining the intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity, the method further comprises: constructing an intermuscular pressure change curve of the target muscle group according to the intermuscular pressure change information of the target muscle group in different states; analyzing the intermuscular pressure change curve to obtain an analysis result of the intermuscular pressure change curve, and evaluating the mechanical function and health status of the target muscle group according to the analysis result.

4. The method of claim 1, wherein, The method of obtaining the intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity comprises: substituting the second shear wave group velocity or the second phase velocity into the shear wave velocity-intermuscular pressure relationship to obtain an active force level of the target muscle group in different states; determining the intermuscular pressure of the target muscle group in each state according to the active force level, so as to obtain the intermuscular pressure change information in different states through the intermuscular pressure in each state.

5. An apparatus for measuring intermuscular pressure based on shear wave mechanical imaging, characterized in that, The method comprises: a establishing module configured to establish a constitutive equation of active mechanical behavior corresponding to a target muscle group of a target subject, and determine a stress-strain relationship, a shear wave group velocity function and an intermuscular pressure function of the target muscle group according to the constitutive equation; a measuring module configured to measure, based on the constitutive equation, an elastic modulus of the target muscle group in a preset initial state, a first shear wave group velocity or a first phase velocity of the target subject in a target posture when the target subject is in an external pressure-free state, and a second shear wave group velocity or a second phase velocity of the target subject in the target posture when the target subject is in an external pressure state; a determining module configured to determine, based on the shear wave group velocity function, the intermuscular pressure function, the first shear wave group velocity or the first phase velocity, a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relationship, so as to obtain intermuscular pressure change information of the target muscle group in different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity. The determining module is configured to determine a plurality of undetermined parameters and a shear wave velocity-interstitial pressure relationship of the constitutive equation based on the shear wave group velocity function, the interstitial pressure function, the first shear wave group velocity, or the first phase velocity, so as to obtain the interstitial pressure change information of the target muscle group in different states according to the shear wave velocity-interstitial pressure relationship, the second shear wave group velocity, or the second phase velocity.

6. The apparatus of claim 5, wherein, Further comprising: The execution module is configured to apply a target internal pressure or a target external pressure to the target muscle group through a pre-set pressure strategy before the constitutive equation of the target muscle group of the target subject is established, so that the target muscle group performs a corresponding movement operation according to a pre-set trajectory.

7. The apparatus of claim 5, wherein, Further comprising: The construction module is configured to construct an interstitial pressure change curve of the target muscle group according to the interstitial pressure change information of the target muscle group in different states after the interstitial pressure change information of the target muscle group in different states is obtained according to the shear wave velocity-interstitial pressure relationship, the second shear wave group velocity, or the second phase velocity. The analysis module is configured to analyze the interstitial pressure change curve to obtain an analysis result of the interstitial pressure change curve, and evaluate the mechanical function and health status of the target muscle group according to the analysis result.

8. An electronic device, comprising: Comprising: A memory, a processor, and a computer program stored on the memory and executable on the processor, the processor executes the program to implement the interstitial pressure measurement method based on shear wave mechanical imaging according to any one of claims 1-4.

9. A computer-readable storage medium having stored thereon a computer program, characterized in that, The program is executed by the processor to implement the interstitial pressure measurement method based on shear wave mechanical imaging according to any one of claims 1-4.

10. A computer program product comprising a computer program, characterized in that, The computer program is executed to implement the interstitial pressure measurement method based on shear wave mechanical imaging according to any one of claims 1-4.

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