Intermuscular pressure measuring method and device based on shear wave mechanical imaging

Abstract

The invention relates to an intermuscular pressure measuring method and device based on shear wave mechanical imaging, and the method comprises the steps: building a constitutive equation of an active mechanical behavior, and determining a stress-strain relation of a muscle group, a shear wave group speed function, and an intermuscular pressure function; 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 when the subject is in a state without external pressure under the target posture, and a second shear wave group velocity or a second phase velocity when the subject is in a state with external pressure under the target posture; and determining a plurality of undetermined parameters of the constitutive equation and a shear wave velocity-intermuscular pressure relational expression, 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 in the prior art, nondestructive in-vivo mechanical characterization, continuous monitoring of changes of in-vivo intermuscular pressure, monitoring of intermuscular pressure in multiple areas and the like on specific muscles are difficult to achieve at the same time are solved.

Description

Technical Field

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

[0002] Since skeletal muscle contains a large amount of water, it can be described as a two-phase material. More and more studies have shown that intermuscular pressure (hydrostatic pressure within the muscle, IMP) can effectively reflect the physiological state and functional characteristics of 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 lead to obstruction of blood circulation in the muscle, causing acute ischemic damage to the muscle and nerves and related inflammatory reactions. Accurate evaluation of the intermuscular pressure of skeletal muscle helps to fully model the muscle mechanically, thereby describing the current physiological state of the muscle and its response during active and passive contraction. Based on the comparison of bilateral intermuscular pressure and the comparison of intermuscular pressure between different groups, it can quantitatively evaluate the degree of muscle injury, fatigue, and symmetry, and can also help diagnose muscle injection pain and diseases related to intermuscular pressure, thus playing an important role in sports health, sports rehabilitation, clinical diagnosis and other fields.

[0004] Elastic imaging is a general term for a class of methods for measuring the mechanical properties of tissues in vivo. A typical elastic imaging method includes four steps:

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

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

[0007] 3. Substitute the mechanical excitation signal and the acquired response into a mechanical model that matches the mechanical behavior of the tissue to quantitatively invert the mechanical properties of the tissue;

[0008] 4. Correlate the mechanical parameters of tissues with tissue diseases, and explore the clinical application of elastic imaging methods.

[0009] Typical mechanical parameters measured by elastic imaging include elastic modulus (directly related to hardness, the most important result of elastic imaging), viscoelastic parameters (reflecting tissue viscosity, related to fatty liver, etc.), hyperelastic parameters (reflecting tissue strain hardening behavior), etc. By giving a constitutive relationship (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 tissue biomechanics research and the advancement of various in vivo tissue mechanical response collection methods (such as imaging, sensor technology), elastic imaging methods have continued to develop. Specifically, in terms of intermuscular pressure detection, the existing technologies in clinical and scientific research are as follows:

[0010] 1. Wick catheter technology (such as Figure 1 (a) in the figure): The design principle of the wick catheter is to maintain the patency of the catheter by placing tiny fibers or filaments at the tip of the catheter; given the low fluid content in most tissues, studies on tissue fluid pressure are highly dependent on optimizing the contact between the free fluid in the tissue and the saline in the measurement device.

[0011] The wick catheter fibers ensure fluid continuity and significantly increase the contact area between saline and the catheter filling area; since there is no fluid-gas interface inside or around the wick fibers, capillary phenomena are avoided, allowing immediate recording of tissue fluid pressure. Under normal circumstances, there is no osmotic interaction between tissue fluid and the wick boundary, and even red blood cells can freely pass between the wick fibers; solutes and particles with a diameter greater than 1 micron can be considered osmotic inert in this context. The measurement accuracy of the wick catheter is affected by the wick fiber material (such as cotton, silk, nylon, polyester, etc.) and the tightness of the wrapping. Therefore, the wick catheter must be fully cleaned and disinfected before each measurement.

[0012] 2. Slit catheter technology (such as Figure 1 (b) in the figure): The slit catheter technology is based on a principle similar to that of the wick catheter. The tip of the catheter is specially designed to contain five 30 mm long plastic petal structures that can maintain the patency of the catheter without the infusion of 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, the slit catheter technology also has limitations. Compared with catheters containing wick fibers, these open catheters are more likely to produce bubbles during operation, which may have an adverse effect on the measurement accuracy. Therefore, when using a slit catheter for tissue fluid pressure measurement, special attention should be paid to the generation of bubbles and their potential impact on the measurement results.

[0013] 3. Myopress catheter (such as Figure 1 (c) in the figure): The Myopress catheter system monitors fluid pressure in real time through a hole opened on the side of the catheter, and can exhibit extremely high dynamic motion responsiveness 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 the subject or patient can perform in application, and this method needs to be paid attention to and regulated when used.

[0014] 4. The fiber-optic catheter is a sensor-tip catheter with the notable feature that it is not affected by fluid artifacts when measuring intermuscular pressure. In terms of dynamic responsiveness, the fiber-optic catheter system is comparable to the Myopress system.

[0015] Both can provide highly sensitive real-time monitoring. However, the fiber optic catheter itself is relatively large and must be embedded in a saline-filled catheter for use; compared with other small catheter systems, this larger sheath design may cause relative discomfort to the subject or patient; in addition, the large size of the fiber optic system may also cause a piston effect during movement, that is, positive IMP and negative IMP artifacts generated when the catheter moves, which may affect the accuracy of the measurement results; more seriously, in the case of strenuous or abnormal movement, the optical fiber itself is at risk of breaking, which may lead to measurement interruption or data loss; therefore, when applying the fiber optic catheter system, special attention should be paid to issues such as patient comfort, movement status, and durability of the optical fiber.

[0016] 5. Electronic sensor catheter (such as Figure 1 (d) in the figure): The electronic sensor catheter has a significant advantage in monitoring changes in intermuscular pressure due to its excellent dynamic response performance, and is not interfered by the saline column; however, when the catheter is inserted into the skeletal muscle in the initial stage, negative intermuscular pressure may be observed due to the piston effect because there is usually no fluid in the tissue space; in addition, with the insertion of the catheter and the experimental contraction of the muscle, edema fluid or blood bags are often formed, which may cause local fluctuations in intermuscular pressure during exercise. Therefore, when using electronic sensor catheters for intermuscular pressure monitoring, these potential influencing factors need to be fully considered.

[0017] In summary, with the development of muscle biomechanics research and the advancement of corresponding instruments and equipment, a series of new methods for in vivo characterization of intermuscular pressure have emerged. However, existing technologies make it difficult to simultaneously achieve non-destructive in vivo mechanical characterization of specific muscles, continuous monitoring of changes in in vivo intermuscular pressure, and monitoring of intermuscular pressure in multiple regions, which urgently needs to be solved. Summary of the invention

[0018] The present application provides a method and device for measuring intermuscular pressure based on shear wave mechanical imaging to solve the problems that the existing technology is difficult to simultaneously achieve non-destructive in vivo mechanical characterization of specific muscles, continuous monitoring of changes in in vivo intermuscular pressure, and monitoring of intermuscular pressure in multiple regions.

[0019] The first aspect of the present application provides an intermuscular pressure measurement method based on shear wave mechanical imaging, comprising the following steps: establishing a constitutive equation of the main dynamic behavior corresponding to a target muscle group of a target subject, and determining the stress-strain relationship, shear wave group velocity function and 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 when the target subject is in a state without external pressure in a target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure 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 multiple unknown parameters of the constitutive equation and the shear wave velocity-intermuscular pressure relationship, so as 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.

[0020] Optionally, in one embodiment of the present application, before establishing the constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, it also includes: applying target internal pressure or 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 present 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, it also includes: 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 based on the analysis result.

[0022] Optionally, in one 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 velocity-intermuscular pressure relationship formula, 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 velocity-intermuscular pressure relationship formula to obtain the 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.

[0023] A second aspect of the present application provides an intermuscular pressure measurement device based on shear wave mechanical imaging, comprising: an establishment module, used to establish a constitutive equation of the main dynamic behavior corresponding to a target muscle group of a target subject, and determine the stress-strain relationship, shear wave group velocity function and intermuscular pressure function of the target muscle group according to the constitutive equation; a measurement module, used to measure, 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 a state without external pressure in a target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure in the target posture; a determination module, used to determine multiple unknown 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 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.

[0024] Optionally, in one embodiment of the present application, it also includes: an execution module, which is used to apply target internal pressure or target external pressure to the target muscle group through a preset pressure strategy before establishing the constitutive equation of the main dynamic behavior corresponding to 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 one embodiment of the present application, it also includes: a construction module, which is used to construct 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 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; an analysis module, which is used to analyze the intermuscular pressure change curve to obtain an analysis result of the intermuscular pressure change curve, and evaluate the mechanical function and health status of the target muscle group according to the analysis result.

[0026] Optionally, in one embodiment of the present application, the determination module includes: a substitution unit, used to substitute the second shear wave group velocity or the second phase velocity into the shear wave velocity-intermuscular pressure relationship to obtain the active force level of the target muscle group in different states; a generation unit, used to determine 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.

[0027] A third aspect of the present application provides an electronic device, comprising: a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the program to implement the intermuscular pressure measurement method based on shear wave mechanical imaging as described in the above embodiment.

[0028] The fourth aspect of the present application provides a computer-readable storage medium, which stores a computer program. When the program is executed by a processor, it implements the above-mentioned intermuscular pressure measurement method based on shear wave mechanical imaging.

[0029] The fifth aspect of the present application provides a computer program product, including a computer program, which is executed to implement the above-mentioned intermuscular pressure measurement method based on shear wave mechanical imaging.

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

[0031] The embodiment of the present application can establish the constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, and determine the stress-strain relationship, shear wave group velocity function and intermuscular pressure function of the target muscle group according to the constitutive equation; based on the constitutive equation, measure 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 a state without external pressure in the target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure 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, determine multiple undetermined parameters of the constitutive equation and the shear wave velocity-intermuscular pressure relationship, so as 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, so as to perform real-time, fast and convenient in vivo mechanical characterization of the intermuscular pressure. Thus, the problems that the existing technology is difficult to simultaneously realize non-destructive in vivo mechanical characterization for specific muscles, continuous monitoring of changes in in vivo intermuscular pressure, and monitoring of intermuscular pressure in multiple regions are solved.

[0032] Additional aspects and advantages of the present application will be given in part in the description below, and in part will become apparent from the description below, or will be learned through the practice of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] The above and / or additional aspects and advantages of the present application will become apparent and easily understood from the following description of the embodiments in conjunction with the accompanying drawings, in which:

[0034] Figure 1 (a) is a schematic diagram of a wick conduit provided in one embodiment of the present application;

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

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

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

[0038] Figure 2 A flow chart 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) is a schematic diagram of a passive muscle SWV changing with IMP provided in one embodiment of the present application;

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

[0041] Figure 3 (c) is a schematic diagram showing the influence of a change in a hyperelastic parameter α within a wide range on the relationship between SWV and IMP provided by an embodiment of the present application;

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

[0043] Figure 4 (a) is a schematic diagram of an experiment using a syringe to pressurize a pig skeletal muscle in vitro experiment provided by an embodiment of the present application;

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

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

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

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

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

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

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

[0051] Figure 7 A schematic diagram of the structure of an electronic device provided in an embodiment of the present application.

[0052] Among them, 10-intermuscular pressure measurement device based on shear wave mechanical imaging; 100-establishment module, 200-measurement module, 300-determination module; 701-memory, 702-processor, 703-communication interface. DETAILED DESCRIPTION

[0053] Embodiments of the present application are described in detail below, and examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are intended to be used to explain the present application, and should not be construed as limiting the present application.

[0054] The following describes the intermuscular pressure measurement method and device based on shear wave mechanical imaging according to an embodiment of the present application with reference to the accompanying drawings. In response to the problems mentioned in the above background technology, the present application provides a method for measuring intermuscular pressure based on shear wave mechanical imaging, in which a constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject is established, and the stress-strain relationship, shear wave group velocity function and 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 a state without external pressure in the target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure 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, multiple unknown parameters of the constitutive equation and the shear wave velocity-intermuscular pressure relationship are determined, so as 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, so that the intermuscular pressure can be characterized in real time, quickly and conveniently in vivo. This solves the problem that the existing technology is difficult to simultaneously achieve non-destructive in vivo mechanical characterization of specific muscles, continuous monitoring of changes in intermuscular pressure in vivo, and monitoring of intermuscular pressure in multiple regions.

[0055] Specifically, Figure 1 A flow chart of a method for measuring intermuscular pressure based on shear wave mechanical imaging provided in an embodiment of the present application.

[0056] like Figure 1 As 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 the main dynamic behavior corresponding to the target muscle group of the target subject is established, and the stress-strain relationship, shear wave group velocity function and intermuscular pressure function of the target muscle group are determined according to the constitutive equation.

[0058] The present application embodiment

[0059] 1. Select a constitutive equation suitable for describing the main dynamic behavior of the muscle. 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, which is used to describe the level of active force exerted by the muscle in order to study the intermuscular pressure during active force exertion.

[0062] The constitutive equations 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 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 of the target state of the muscle compared to the initial state of the muscle (which can be converted into strain); in the embodiment of the present application, μ0 of the above two parameters is necessary, and the active parameter ω a The introduction of is to more accurately characterize the active dynamic behavior of the muscle, so as to invert the changes in intermuscular pressure under active force state, but it is not a necessary parameter.

[0069] It should be noted that the embodiment of the present application is also applicable to the inversion of intermuscular pressure under the passive constitutive method. In addition, other parameters need to be added on the basis of these two parameters. In addition, in the actual implementation process, those skilled in the art may also use a certain deformation of the above two parameters (such as using E0=f0=3μ0 as a substitute for the initial elastic modulus) as the basic variable, which is not specifically limited here.

[0070] Therefore, the embodiments of the present application provide reliable theoretical and data support for the subsequent measurement of intermuscular pressure of specific muscles of the human body under specific conditions by selecting a constitutive equation suitable for describing the main dynamic behavior of the muscle.

[0071] Optionally, in one embodiment of the present application, before establishing the constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, it also includes: applying target internal pressure or 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 a preset trajectory.

[0072] It should be noted that before establishing the constitutive equations of the main dynamic behaviors corresponding to the target muscle groups of the target subjects, the embodiments of the present application also require injection or external pressure operation on specific muscle parts of the subjects through methods such as cuffs or syringes, so that muscle groups such as skeletal muscles are subjected to a certain amount of internal or external pressure, thereby making the specific muscle groups move according to a predetermined trajectory, such as keeping the elbow joint at a 90-degree angle at all times.

[0073] Therefore, the embodiments of the present application ensure effective measurement of changes in intermuscular pressure in a specified sequence by causing the specified muscles to move according to the specified sequence.

[0074] In step S102, 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 a state without external pressure in the target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure in the target posture 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, multiple unknown 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 under different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

[0076] After determining the constitutive equation, further, the embodiments of the present application first need to measure the elastic modulus μ0 of the muscle in the initial state through a combination of one or more methods such as muscle hardness meter, static elastic imaging, shear wave elastic imaging, etc.; wherein the initial state is defined as a state in which the muscle has no active force and no external pressure, and in principle, the initial state should be a state in which the passive stretch of the muscle is minimal.

[0077] Secondly, in the embodiment of the present application, when the subject is in the target posture and no external pressure is applied, the shear wave group velocity or phase velocity (ie, the first shear wave group velocity or the first phase velocity) c0 of the muscle in the target posture is measured.

[0078] Again, the embodiment 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) of the muscle in the target posture when the subject is in the target posture and external pressure is applied. p .

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

[0080] Optionally, in one 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 velocity-intermuscular pressure relationship formula, 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 velocity-intermuscular pressure relationship formula to obtain the 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.

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

[0082] Therefore, the embodiments of the present application can perform in vivo mechanical characterization on specific muscles individually and can non-destructively and quantitatively measure the intermuscular pressure of the muscles.

[0083] Optionally, in one 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 velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity, it also includes: 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 based on the analysis result.

[0084] It should be noted that after obtaining the intermuscular pressure change information of the target muscle group under different states, the embodiments of the present application evaluate the mechanical function and health status of the muscle by analyzing the change curve of the intermuscular pressure in the sequence, and display the change curve of the intermuscular pressure of the muscle in the specified sequence through an electronic display screen, printer, etc., or further analysis results of the curve (such as extreme values), so as to monitor the changes in the intermuscular pressure in the body in real time.

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

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

[0087] Among them, the muscle pressure module: This module can make a specific muscle group bear a specified load, for example, the skeletal muscle can be subjected to a quantitative internal or external pressure through a cuff or a syringe;

[0088] Muscle motion constraint module: This module enables specific muscle groups to move along a predetermined trajectory. For example, the elbow joint can be kept at a 90-degree angle by using a limit unit or a servo motor.

[0089] Muscle shear wave excitation module: This module can excite shear waves in the muscles, for example, by driving a mechanical structure through a motor to achieve reciprocating vibration, and the vibration contacts the skin, thereby exciting shear waves in the muscles; the shear wave excitation module can be realized by generating ultrasonic radiation force by a motor or piezoelectric ceramics or focused ultrasound;

[0090] Muscle shear wave acquisition module: collects shear waves propagating in the muscle and obtains the group velocity / phase velocity of the shear wave propagation, for example, by high frame rate ultrasound imaging (which can be achieved by ultrasound imaging, magnetic resonance imaging and other imaging methods or vibration sensors) 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 states, the intermuscular pressure is fitted by the least square method and other methods;

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

[0093] The following is a specific embodiment combined with the accompanying drawings, and takes the human biceps brachii as an example to illustrate the execution process of the intermuscular pressure measurement method and system based on shear wave mechanical imaging of the present application.

[0094] First, the constitutive equation suitable for describing the active dynamic behavior of the muscle is selected. Here, the active constitutive model of muscle proposed by Ehret in 2011 is selected, and the expression of its strain energy function is:

[0095]

[0096] Among them, μ, α, and β represent material parameters. μ is the initial shear modulus, α and β represent the hyperelastic hardening index of muscle fibers. m represents the direction of muscle fibers, and the invariant and It is related to the right Cauchy-Green strain tensor C and the fiber structure tensor M = mm, and its expression is:

[0097]

[0098]

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

[0100] Among them, w0, w p They represent the weight factors related to the isotropic tissue component of the muscle and the muscle fiber component respectively. The main advantage of this constitutive model is that it defines an effective muscle active parameter w a Once w is determined a , the current activation state of the muscle can be determined, and the stress can also be obtained from the constitutive equation (7). i (i=1~5) is the invariant 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, the present application can further derive the calculation expression of stress in the muscle as follows:

[0102]

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

[0104]

[0105]

[0106] It should be noted that under this constitutive model, the relationship between the shear wave velocity and each constitutive parameter is as follows: Figure 3 As shown, Figure 3 (a) shows the sensitivity of shear wave velocity to IMP. When IMP changes from 0 to 100 mmHg, the shear wave velocity in the passive state (w a =0) increased by about 2.5 times; Figure 3 (b) shows different active parameters w a The shear wave velocity changes with w a This indicates that both active muscle contraction and the increase in IMP lead to a significant increase in shear wave velocity. Figure 3 (c) and Figure 3 (d) in Figure 1 highlights the variation of SWV with IMP for different hyperelastic parameters α and β. It can be seen that the variation of α and β over a large range has no significant effect on SWV. This result shows that when inferring IMP from measured shear waves, the present application only needs the population reference values ​​of α and β to invert the intermuscular pressure, thus greatly simplifying the inversion method.

[0107] In order to verify the relevant theories of the intermuscular pressure measurement method based on shear wave mechanical imaging of the present application, the present application can conduct in vitro experiments and in vivo experiments on pig skeletal muscle and human biceps brachii to determine the intermuscular pressure.

[0108] In the in vitro experiment of pig skeletal muscle, the present application can use pig skeletal muscle obtained from the legs of freshly slaughtered animals. The fresh pig skeletal muscle is kept between 2°C and 4°C in an ice box and then transported to the laboratory. After thawing for two hours at room temperature, a large uniform area is selected for the experiment. In order to directly measure the IMP corresponding to each pressure level, a pressure system (Transonic SP200) is used. The system consists of a pressure catheter and a power amplifier. After completing the initial shear wave velocity measurement of the pig skeletal muscle, the pressure catheter is immersed in clean water for cleaning, and the pressure value is calibrated after drying. After calibration, the pressure catheter is placed in a needle with a diameter of 0.8 mm and inserted into the surface of the pig skeletal muscle for about 2 cm, and then the needle is slowly pulled out, such as Figure 4 As shown in (a); when the residual stress is completely released, a syringe filled with water is inserted into the muscle about 8 mm from the pressure catheter, and the syringe is pushed slowly and evenly while monitoring the changes in the pressure catheter reading at 20, 40, 60, 80, and 100 mmHg. At each pressure, the Verasonics system is used to stimulate the acoustic radiation force and obtain the ultrasonic signal; at each pressure, 5 SWV measurements are performed along the muscle fiber.

[0109] Figure 4 (b) in Figure 3 illustrates the IMP inferred using the method given above; Figure 4 (c) and Figure 4 (d) in the figure summarizes the SWV of pig skeletal muscle before and after compression, in which the SWV of pig skeletal muscle increased significantly with the increase of IMP; Figure 3 The analysis shows that the change of α and β within a certain range has no significant effect on the shear wave velocity. Therefore, the present application infers the intermuscular pressure of pig skeletal muscle by pre-setting α=6.3, β=5.2, and measures the initial shear modulus μ=7.01kPa by the shear wave velocity of pig skeletal muscle in the initial state. It can be seen that the IMP obtained by the inverse problem is close to the value directly measured by the pressure catheter, which shows that this method can effectively invert the intermuscular pressure of pig skeletal muscle in different states in vitro.

[0110] In order to verify the effectiveness of the theory and method of the present application for in vivo skeletal muscle intermuscular pressure inversion, the present application further conducted an in vivo experiment on the biceps of a healthy male volunteer (age: 26 years old, height: 169.0 cm, weight: 66.6 kg). The subject gave informed consent after a detailed explanation of the nature and possible consequences of the study.

[0111] First, this application measures the passive parameters of the biceps brachii. The volunteers wore an elbow fixation brace (Ober, EO-30 model), placed their arms on the table and were in a relaxed state. The elbow flexion angle was adjusted to 90° using the elbow fixation brace. Five shear wave velocity measurements were obtained along the muscle fibers, and the passive parameters were inferred using Formula 1.8. α and β can still use the pre-set α=6.3 and β=5.2.

[0112] Using the derived passive muscle parameters, the present application can obtain the correlation between shear wave velocity and intermuscular pressure, and then evaluate the IMP of the biceps brachii at different cuff pressures, place the biceps brachii in a relaxed position on the table, and measure the initial SWV; then, tie a mercury sphygmomanometer cuff on the upper end of the biceps brachii, such as Figure 5 As shown in (a), the pressure was quickly increased to 40 mmHg, maintained for 30 seconds, and the shear wave velocity was measured; then the air valve was opened to release the pressure, and the volunteer was allowed to rest for two minutes; the above steps were repeated to measure the shear wave velocity when the cuff pressure was 80 and 120 mmHg, and 5 shear wave velocities were obtained at each pressure. The B-ultrasound images were monitored in real time to confirm that there was no obvious muscle movement. Based on the measured SWV, the IMP under different cuff pressures was inferred, as shown in Figure 1. Figure 5 As shown in (c) in .

[0113] In addition, the present application detected the shear wave velocity of the biceps brachii under different cuff pressures, and used equations (8) and (9) to invert the IMP in vivo. The results are as follows: Figure 5 As shown in (b), it can be seen that the muscle shear wave velocity increases with the increase of cuff pressure. The in vivo change of IMP is increased by 14.9 mmHg through cuff pressurization, which shows that the intermuscular pressure testing method of the present application can not only measure the passive dynamic parameters of the muscle for the evaluation of the muscle state of the volunteers, but its in vivo measurement of intermuscular pressure can more conveniently and effectively evaluate the muscle function of the volunteers under different physiological states.

[0114] The following is a brief explanation of the relevant modules of the intermuscular pressure measurement system based on shear wave mechanical imaging used in this application. The muscle pressure module in the above specific embodiment is realized by a syringe when out of body and cuff pressurization when in body, thereby completing the shear wave velocity collection of the muscle under different physiological states; the muscle movement constraint module is a bracket for fixing the elbow joint, which can accurately control the elbow flexion angle of the volunteer; the excitation of muscle shear waves is achieved by focusing the acoustic radiation force, and the Verosonics fast imaging system is used to realize high frame rate ultrasound image acquisition; the intermuscular pressure model and inversion method are mainly realized by equations (8) and (9), and finally the fitting statistics are obtained Figure 4 and Figure 5As shown in the results, this specific embodiment achieves in vivo measurement of intermuscular pressure for the biceps brachii of the human body, thereby realizing functional evaluation and disease detection of muscles under various physiological states.

[0115] According to the intermuscular pressure measurement method based on shear wave mechanical imaging proposed in the embodiment of the present application, a constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject is established, and the stress-strain relationship, shear wave group velocity function and 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 a state without external pressure in the target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure 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, multiple unknown parameters of the constitutive equation and the shear wave velocity-intermuscular pressure relationship are determined, so as 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, so that the intermuscular pressure can be characterized in real time, quickly and conveniently in vivo.

[0116] Secondly, the intermuscular pressure measurement device based on shear wave mechanical imaging proposed in accordance with an embodiment of the present application is described with reference to the accompanying drawings.

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

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

[0119] Among them, the module 100 is established to establish the constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, and determine the stress-strain relationship, shear wave group velocity function and intermuscular pressure function of the target muscle group according to the constitutive equation.

[0120] The measurement module 200 is used to measure 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 a state without external pressure in a target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure in a target posture based on the constitutive equation.

[0121] Determination module 300 is used to determine multiple unknown parameters of the constitutive equation and the 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 the intermuscular pressure change information of the target muscle group under different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

[0122] Optionally, in one embodiment of the present application, the intermuscular pressure measurement device 10 based on shear wave mechanical imaging of the embodiment of the present application also includes: an execution module, which is used to apply target internal pressure or target external pressure to the target muscle group through a preset pressure strategy before establishing the constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, so that the target muscle group performs corresponding movement operations according to the preset trajectory.

[0123] Optionally, in one embodiment of the present application, the intermuscular pressure measurement device 10 based on shear wave mechanical imaging of the embodiment of the present application further includes: a construction module and an analysis module.

[0124] Among them, the construction module is used to construct the intermuscular pressure change curve of the target muscle group according to the intermuscular pressure change information of the target muscle group under different states after obtaining the intermuscular pressure change information of the target muscle group under different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

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

[0126] Optionally, in one embodiment of the present application, the determination module 200 includes: a substitution unit and a generation unit.

[0127] The substitution unit is used to substitute the second shear wave group velocity or the second phase velocity into the shear wave velocity-intermuscular pressure relationship to obtain the active force level of the target muscle group under different states.

[0128] The generating unit is used to determine 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.

[0129] It should be noted that the aforementioned explanation of the embodiment of the intermuscular pressure measurement method based on shear wave mechanical imaging is also applicable to the intermuscular pressure measurement device based on shear wave mechanical imaging of this embodiment, and will not be repeated here.

[0130] According to the intermuscular pressure measurement device based on shear wave mechanical imaging proposed in the embodiment of the present application, the device includes an establishment module for establishing a constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, and determining the stress-strain relationship, shear wave group velocity function and intermuscular pressure function of the target muscle group according to the constitutive equation; a measurement module for 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 when the target subject is in a state without external pressure in the target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure in the target posture based on the constitutive equation; a determination module for determining multiple unknown parameters of the constitutive equation and the 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 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, so as to enable real-time, rapid and convenient in vivo mechanical characterization of the intermuscular pressure.

[0131] Figure 7 A schematic diagram of the structure of an electronic device provided in an embodiment of the present application. The electronic device may include:

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

[0133] When the processor 702 executes the program, the intermuscular pressure measurement method based on shear wave mechanical imaging provided in the above embodiment is implemented.

[0134] Furthermore, the electronic device further comprises:

[0135] The communication interface 703 is used for communication between the memory 701 and the processor 702 .

[0136] The memory 701 is used to store computer programs that can be executed on the processor 702 .

[0137] The memory 701 may include a high-speed RAM memory, and may also include a non-volatile memory (non-volatile memory), such as 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 to each other through a bus and communicate with 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. The bus can be divided into an address bus, a data bus, a control bus, etc. For ease of representation, Figure 7 Only one thick line is used in the diagram, but this 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 communicate with each other through an internal interface.

[0140] The processor 702 may be a central processing unit (CPU), or an application specific integrated circuit (ASIC), or one or more integrated circuits configured to implement the embodiments of the present application.

[0141] An embodiment of the present application also provides a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the above-mentioned method for measuring intermuscular pressure based on shear wave mechanical imaging.

[0142] An embodiment of the present application also provides a computer program product, including a computer program, which, when executed, is used to implement the above-mentioned intermuscular pressure measurement method based on shear wave mechanical imaging.

[0143] In the description of this specification, the description with reference to the terms "one embodiment", "some embodiments", "example", "specific example", or "some examples" etc. means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present application. In this specification, the schematic representations of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described may be combined in any one or N embodiments or examples in a suitable manner. In addition, those skilled in the art may combine and combine the different embodiments or examples described in this specification and the features of the different embodiments or examples, without contradiction.

[0144] In addition, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include at least one of the features. In the description of this application, "N" means at least two, such as two, three, etc., unless otherwise clearly and specifically defined.

[0145] Any process or method description in a flowchart or otherwise described herein may be understood to represent a module, fragment or portion of code comprising one or N executable instructions for implementing the steps of a custom logical function or process, and the scope of the preferred embodiments of the present application includes alternative implementations in which functions may not be performed in the order shown or discussed, including performing functions in a substantially simultaneous manner or in reverse order depending on the functions involved, which should be understood by technicians in the technical field to which the embodiments of the present application belong.

[0146] The logic and / or steps represented in the flowchart or otherwise described herein, for example, can be considered as an ordered list of executable instructions for implementing logical functions, and can be embodied in any computer-readable medium for use by an instruction execution system, device or apparatus (such as a computer-based system, a system including a processor, or other system that can fetch instructions from an instruction execution system, device or apparatus and execute instructions), or in combination with these instruction execution systems, devices or apparatuses. For the purpose of this specification, "computer-readable medium" can be any device that can contain, store, communicate, propagate or transmit a program for use by an instruction execution system, device or apparatus, or in combination with these instruction execution systems, devices or apparatuses. More specific examples of computer-readable media (a non-exhaustive list) include the following: an electrical connection with one or N wirings (electronic devices), a portable computer disk box (magnetic device), a random access memory (RAM), a read-only memory (ROM), an erasable and programmable read-only memory (EPROM or flash memory), a fiber optic device, and a portable compact disk read-only memory (CDROM). In addition, the computer-readable medium may even be paper or other suitable medium on which the program is printed, since the program may be obtained electronically by optically scanning the paper or other medium and then editing, interpreting or processing in other suitable ways as necessary and then storing it in a computer memory.

[0147] It should be understood that the various parts of the present application can be implemented by hardware, software, firmware or a combination thereof. In the above embodiment, the N steps or methods can be implemented by software or firmware stored in a memory and executed by a suitable instruction execution system. If implemented by hardware, as in another embodiment, it can be implemented by any one of the following technologies known in the art or their combination: a discrete logic circuit having a logic gate circuit for implementing a logic function for a data signal, a dedicated integrated circuit having a suitable combination of logic gate circuits, a programmable gate array (PGA), a field programmable gate array (FPGA), etc.

[0148] A person skilled in the art may understand that all or part of the steps in the method for implementing the above-mentioned embodiment may be completed by instructing related hardware through a program, and the program may be stored in a computer-readable storage medium, which, when executed, includes one or a combination of the steps of the method embodiment.

[0149] In addition, each functional unit in each embodiment of the present application may be integrated into a processing module, or each unit may exist physically separately, or two or more units may be integrated into one module. The above-mentioned integrated module may be implemented in the form of hardware or in the form of a software functional module. If the integrated module is implemented in the form of a software functional module and sold or used as an independent product, it may also be stored in a computer-readable storage medium.

[0150] The storage medium mentioned above may 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 can be understood that the above embodiments are exemplary and cannot be understood as limiting the present application. A person of ordinary skill in the art may change, modify, replace and modify the above embodiments within the scope of the present application.

Claims

1. A method for measuring intermuscular pressure based on shear wave mechanical imaging, characterized in that: The following steps are involved: Establishing a constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, and determining the stress-strain relationship, shear wave group velocity function and 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 when the target subject is in a state without external pressure in the target posture, and the second shear wave group velocity or the second phase velocity when the target subject is in a state with external pressure 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, multiple unknown parameters of the constitutive equation and the shear wave velocity-intermuscular pressure relationship are determined, so as to obtain the intermuscular pressure change information of the target muscle group under 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 according to claim 1, characterized in that Before establishing the constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, the method further includes: A target internal pressure or a target external pressure is applied to the target muscle group through a preset pressure strategy, so that the target muscle group performs a corresponding movement operation according to the preset trajectory.

3. The method according to claim 1, characterized in that 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 includes: 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; The intermuscular pressure change curve is analyzed to obtain an analysis result of the intermuscular pressure change curve, and the mechanical function and health status of the target muscle group are evaluated according to the analysis result.

4. The method according to claim 1, characterized in that 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 includes: Substituting the second shear wave group velocity or the second phase velocity into the shear wave velocity-intermuscular pressure relationship to obtain the active force level of the target muscle group under different states; The intermuscular pressure of the target muscle group in each state is determined 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. A device for measuring intermuscular pressure based on shear wave mechanical imaging, characterized in that: include: Establishing a module for establishing a constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, and determining the stress-strain relationship, shear wave group velocity function and intermuscular pressure function of the target muscle group according to the constitutive equation; A measurement module, for measuring, based on the constitutive equation, the 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 a state without external pressure in a target posture, and a second shear wave group velocity or a second phase velocity when the target subject is in a state with external pressure in the target posture; A determination module is used to determine multiple unknown 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 the intermuscular pressure change information of the target muscle group under different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity.

6. The device according to claim 5, characterized in that Also includes: An execution module is used to apply target internal pressure or target external pressure to the target muscle group through a preset pressure strategy before establishing the constitutive equation of the main dynamic behavior corresponding to the target muscle group of the target subject, so that the target muscle group performs corresponding movement operations according to the preset trajectory.

7. The device according to claim 5, characterized in that Also includes: A construction 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 under different states after obtaining the intermuscular pressure change information of the target muscle group under different states according to the shear wave velocity-intermuscular pressure relationship, the second shear wave group velocity or the second phase velocity; The analysis module is used to analyze the intermuscular pressure change curve to obtain the analysis result of the intermuscular 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, characterized in that: include: A memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the program to implement the intermuscular pressure measurement method based on shear wave mechanical imaging as described in any one of claims 1 to 4.

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

10. A computer program product, comprising a computer program, characterized in that The computer program is executed to implement the method for measuring intermuscular pressure based on shear wave mechanical imaging as described in any one of claims 1 to 4.

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