System comprising controller and electrical stimulation system

Abstract

The present disclosure provides a controller and method for providing signaling to an ES system to operate an electrode array in a detection mode to cause the ES system to provide a plurality of electrical parameter detection burst sequences, where each electrical parameter detection burst sequence is configured to not provide muscle stimulation; and detecting one or more detection parameters indicative of a degree of activity of the muscle associated with each electrical parameter detection burst sequence, where each electrical parameter detection burst sequence is provided by applying a potential difference between different pairs of the plurality of electrodes, wherein the controller is configured to calculate the electrical parameter between each pair of detection electrodes based on one or more detection parameters. The present disclosure also relates to an associated electrical stimulation system and a computer readable medium.

Description

Technical Field

[0001] This disclosure relates to a controller for an electrical stimulation (ES) system and a corresponding ES system. Background Technology

[0002] Lack of physical activity is becoming one of the greatest health challenges of our time. This problem is particularly acute for medical patients who require immobilization. Immobilization and muscle inactivity can lead to serious medical conditions such as muscle wasting, diabetes, pain, overweight, edema, deep vein thrombosis, and pulmonary embolism, all of which can cause suffering and death. These medical conditions impose enormous healthcare costs, but are likely preventable.

[0003] Treatment for immobilization requires mobilization, i.e., physical activity, which may not be done in the right amount and is not always possible for some people. In short, the inefficiency of interventions is caused by low adherence to treatment. One treatment for activating immobilized muscles is neuromuscular electrical stimulation (NMES) (an example of electrical stimulation (ES) techniques), which is used by physical therapists and, to a lesser extent, by end-users to stimulate inactive skeletal muscles.

[0004] Effective application of NMES requires the electrodes to be correctly positioned at so-called motor points to achieve the most comfortable and energy-efficient muscle stimulation. While motor points tend to be in similar locations among individuals, their exact location can vary considerably between individuals. Furthermore, even the location of individual motor points within a single user may change from one time to another. Electrode matrices can be used to stimulate nerves or muscles at body sites. Measuring such stimulation requires the addition of sensors, such as flexible sensors or other sensors, to detect movement at that body site. Balancing sensitivity with accuracy and flexibility in applying stimulation can be challenging because adding appropriate sensors may encroach on the space that would otherwise be available for electrodes in the electrode matrix. Summary of the Invention

[0005] According to a first aspect of this disclosure, a controller is provided for providing signal transmission to and receiving signal transmission from at least one electrical stimulation (ES) system, the ES system comprising an electrode array including a plurality of electrodes for applying electrical stimulation to a user's muscles, and wherein the electrodes are further configured to measure electrical parameters between any one electrode of the electrode array and any other electrode of the electrode array, wherein the controller is configured to: provide signal transmission to the ES system to operate the electrode array in a detection mode during a detection period, the signal transmission causing the ES system to provide a plurality of electrical parameter detection burst pulse sequences, wherein each electrical parameter detection burst pulse sequence includes one or more detection pulses, and wherein each electrical parameter detection burst pulse sequence is... The system is configured not to provide muscle stimulation; and to detect one or more detection parameters indicating the degree of muscle activity associated with each electrical parameter detection burst pulse sequence, wherein each electrical parameter detection burst pulse sequence is provided by applying a potential difference between different pairs of the plurality of electrodes, wherein an electrode pair refers to a combination of a first detection electrode and a second detection electrode selected from any electrode array, such that when the controller provides a subsequent electrical parameter detection burst pulse sequence, the corresponding electrode pair for the subsequent electrical parameter detection burst pulse sequence includes any two electrode pairs of the electrode array, except for any electrode pairs corresponding to a previously provided electrical parameter detection burst pulse sequence of the detection period, wherein the controller is configured to calculate the electrical parameter between each pair of detection electrodes based on the one or more detection parameters.

[0006] It should be understood that not providing muscle stimulation means applying a sequence of electrical parameters to detect bursts of pulses with an intensity sufficient to induce muscle activation. It should be understood that muscle activity is the amount of muscle movement and may include zero movement. That is, the detected parameters may indicate whether the muscle is moving or the degree of movement. In some embodiments, muscle or body activity is a response to muscle stimulation induced by a stimulation pulse.

[0007] In one or more embodiments, the controller may be configured to provide a signal to the ES system to operate the electrode array in a stimulation mode, the signal causing the ES system to provide a plurality of stimulation pulses separated by rest periods, wherein: each stimulation pulse includes applying a stimulation potential difference between a first stimulation electrode and a second stimulation electrode of the electrode array, such that the stimulation potential difference is configured to provide stimulation to the muscle; and each rest period includes a period of time in which no stimulation pulses are present.

[0008] In one or more embodiments, the detection period may occur during the rest period, such that one or more detection parameters are measured between the application of stimulation pulses.

[0009] In one or more embodiments, the controller may be configured to provide signaling to the ES system such that the ES system provides electrical parameter detection burst pulse sequences between at least 50% of the definable detection electrode pairs within the electrode array, and correspondingly detects one or more detection parameters indicating the degree of bodily activity associated with each electrical parameter detection burst pulse sequence.

[0010] In some alternative embodiments, the controller can be configured to provide signaling to the ES system to provide electrical parameter detection burst pulse sequences among at least 30%, at least 40%, at least 60%, at least 70%, at least 80%, at least 90%, or at least 100% of the definable detection electrode pairs within the electrode array, and correspondingly detect one or more detection parameters indicating the degree of bodily activity associated with each electrical parameter detection burst pulse sequence. By acquiring a large number of measurements among the different electrode pairs definable within the array, a corresponding number of sensors are effectively created that provide improved accuracy, reliability, and position specificity compared to, for example, using a small number of flexible sensors.

[0011] In one or more embodiments, the controller may be further configured to determine, based on electrical parameters calculated between each pair of detection electrodes, whether to provide a signal to the ES system to enable the electrode array to operate in detection mode or alternative mode.

[0012] In one or more embodiments, the detection parameter can be a corresponding electrical parameter to detect the current between electrode pairs during a burst pulse sequence.

[0013] In one or more embodiments, the calculated electrical parameters can be at least one of the following: resistivity; resistance; conductivity; conductance; impedance; and admittance.

[0014] In one or more embodiments, the controller may be further configured to generate an electrical parameter map representing the spatial distribution of electrodes in the electrode array, wherein the electrical parameter map includes a plurality of elements arranged in a grid, and wherein each element includes an element value based on one or more electrical parameters calculated by the controller.

[0015] In one or more embodiments, each element of the electrical parameter map may correspond to an electrode of the electrode array, and the element value of the element of the electrical parameter map is based on the sum of the calculated electrical parameters using the corresponding electrode.

[0016] In one or more embodiments, each element of the electrical parameter map may correspond to an electrode of the electrode array, and the element value of the electrical parameter map is based on the average value of each calculated electrical parameter using the corresponding electrode.

[0017] In one or more embodiments, the controller may be configured to obtain an electrical parameter map of the electrodes of an electrode array obtained during the current detection period, wherein the element values ​​of the electrical parameter map are based on the difference between element values ​​calculated during the current detection period and one of the following: element values ​​calculated during a previous detection period obtained at a time earlier than the current detection period; and predefined element values.

[0018] In one or more embodiments, each element of the electrical parameter map may correspond to an electrode pair of the electrode array, and the element value of the electrical parameter is based on the difference between the electrical parameters calculated between the electrode pairs during the electrical parameter detection burst pulse sequence and the electrical parameters calculated between the electrode pairs during a previous electrical parameter detection burst pulse sequence.

[0019] In one or more embodiments, the controller may be further configured to determine, based on an electrical parameter diagram, whether to provide signaling to the ES system to enable the electrode array to operate in a detection mode or an alternative mode.

[0020] In one or more embodiments, the electrical parameter detection burst pulse sequence may include multiple detection pulses, each detection pulse having a pulse frequency between 10 Hz and 100 MHz.

[0021] In one or more embodiments, the current provided between each pair of detection electrodes for detecting parameters may not exceed 0.1 mA.

[0022] In one or more embodiments, the controller may be configured to cause the ES system to apply multiple skin resistance-reducing pulses during the stimulation period, wherein the skin resistance-reducing pulses include a higher frequency and lower intensity compared to multiple stimulation pulses.

[0023] In one or more embodiments, multiple skin resistance reduction pulses may be superimposed on multiple stimulation pulses.

[0024] In one or more embodiments, the skin resistance reduction pulse may: carry a current of no more than 0.1 mA per pulse; and have a frequency between 1 Hz and 100,000 Hz.

[0025] In one or more embodiments, the controller may be configured to cause the ES system to apply a plurality of sensory blocking pulses when operating in stimulation mode, wherein the sensory blocking pulses have an intensity lower than that of the stimulation pulses.

[0026] In one or more embodiments, the sensory blocking pulse may have a frequency between 0.1 Hz and 150 Hz.

[0027] According to a second aspect of this disclosure, an electrical stimulation (ES) system is provided for receiving signal transmissions from and providing signal transmissions to a controller according to the first aspect.

[0028] In one or more embodiments, the ES system according to the second aspect may further include clothing, wherein the clothing provides support for the relative arrangement of electrodes in the electrode array and is configured to distribute the electrodes on at least one body part of the user.

[0029] According to a third aspect of this disclosure, a computer-readable medium is provided that includes computer program code, the computer-readable medium being configured to cause a controller to operate according to the first aspect or the second aspect.

[0030] According to a fourth aspect of this disclosure, a method is provided for providing electrical stimulation (ES) to a user's muscles using at least one ES system, the ES system comprising a controller and an electrode array including a plurality of electrodes for applying electrical stimulation to the muscles, and wherein the electrodes are further configured to measure electrical parameters between any one electrode of the electrode array and any other electrode of the electrode array, the method comprising the steps of: the controller providing a signal transmission to the ES system to operate the electrode array in a detection mode during a detection period, the signal transmission causing the ES system to provide a plurality of electrical parameter detection burst pulse sequences during at least one detection period, wherein each electrical parameter detection burst pulse sequence includes one or more detection pulses, and wherein each electrical parameter detection burst pulse sequence is configured to... The controller is set to not provide muscle stimulation; and the controller detects one or more detection parameters indicating the degree of muscle activity associated with each electrical parameter detection burst pulse sequence, wherein each electrical parameter detection burst pulse sequence is provided by applying a potential difference between different pairs of the plurality of electrodes, wherein an electrode pair refers to a combination of a first detection electrode and a second detection electrode selected from any electrode array, such that when the controller provides a subsequent electrical parameter detection burst pulse sequence, the corresponding electrode pair for the subsequent electrical parameter detection burst pulse sequence includes any two electrode pairs of the electrode array, except for any electrode pairs corresponding to the previously provided electrical parameter detection burst pulse sequence of the detection period; and the controller calculates the electrical parameters between each pair of detection electrodes based on one or more detection parameters.

[0031] In one or more embodiments, the method according to the fourth aspect may further include the following steps: the controller provides a signal to the ES system to operate the electrode array in a stimulation mode, the signal causing the ES system to provide a plurality of stimulation pulses separated by rest periods, wherein: each stimulation pulse includes applying a stimulation potential difference between a first stimulation electrode and a second stimulation electrode of the electrode array, such that the stimulation potential difference is configured to provide stimulation to the muscle; and each rest period includes a period of time during which no stimulation pulses are present.

[0032] According to a fifth aspect of this disclosure, a controller is provided for providing signal transmission to and receiving signal transmission from at least one system, the system comprising an electrode array including a plurality of electrodes, and wherein the electrodes are further configured to measure electrical parameters between any one electrode of the electrode array and any other electrode of the electrode array, wherein the controller is configured to: provide signal transmission to the system to operate the electrode array in a detection mode during a detection period, the signal transmission causing the system to provide a plurality of electrical parameter detection burst pulse sequences, wherein each electrical parameter detection burst pulse sequence includes one or more detection pulses, and wherein each electrical parameter detection burst pulse sequence is configured not to provide muscle stimulation; and to detect finger... The controller provides one or more detection parameters associated with the activity of the muscle in each electrical parameter detection burst pulse sequence, wherein each electrical parameter detection burst pulse sequence is provided by applying a potential difference between different pairs of the plurality of electrodes, wherein an electrode pair refers to a combination of a first detection electrode and a second detection electrode selected from any electrode array, such that when the controller provides a subsequent electrical parameter detection burst pulse sequence, the corresponding electrode pair for the subsequent electrical parameter detection burst pulse sequence includes any two electrode pairs of the electrode array, except for any electrode pairs corresponding to a previously provided electrical parameter detection burst pulse sequence of the detection period, wherein the controller is configured to calculate the electrical parameter between each pair of detection electrodes based on the one or more detection parameters. In one or more instances, the controller according to the fifth aspect can be a controller for a sensing system configured to sense muscle movement (i.e., muscle stimulation), whether the muscle movement is induced by intentional user movement, unconscious user movement, or movement caused by an external stimulation device. The following description of the stimulation system provides for this disclosure; however, it should be understood that any part of this disclosure that is not inherently related to the generation of stimulation can be similarly implemented in a sensing system for sensing muscle movement, such as the sensing system described in the fifth aspect.

[0033] Although this disclosure can be described in conjunction with NMES treatment, as described in the background section, other applications are also envisioned. Accurate, low-cost motion detection is required in many industries.

[0034] One example is the gaming and simulation industry, particularly virtual reality (VR) and augmented reality (AR) games. Embodiments of this disclosure can be used to capture motion in one or more areas of a user's body. The motion capture data is then processed and used as input to the control feedback loop of the game interface. This provides the user with a more immersive gaming experience. Embodiments of this disclosure can be integrated into clothing or other wearable devices worn by the user while playing the game. Some embodiments of this disclosure can be configured to provide gentle electrical stimulation to the user as part of the control feedback loop of the game interface. For example, if an area of ​​the user's avatar in the game is injured, gentle electrical stimulation can be applied to the corresponding area of ​​the user's body to alert the user to the injury.

[0035] In another instance, embodiments of this disclosure can be used in conjunction with motion enhancement systems, such as powered exoskeletons. Exoskeletons are increasingly used in military, industrial, and medical applications to provide structural support for a user's body. They can enhance a user's strength and endurance, or assist injured or disabled users in movement. Embodiments of this disclosure can be used to capture motion in one or more areas of a user's body. The motion capture data is then processed and used as input to the control feedback loop of the powered exoskeleton, enabling the user to control the exoskeleton using their own body. In some embodiments, the system is configured to provide mild electrical stimulation to the user's body and provide feedback from the powered exoskeleton. For example, the user can be alerted to contact forces applied to the exterior of the exoskeleton by applying mild electrical stimulation to corresponding areas of the user's body. Electrode arrays can be integrated into flexible materials and clothing, such as those used in the latest generation of "soft" exoskeletons (also known as powered clothing). Attached Figure Description

[0036] One or more embodiments will now be described by way of example only with reference to the accompanying drawings, in which: Figure 1 An exemplary embodiment of a system of this disclosure, including a controller and an ES system, is shown; Figure 2 An exemplary representation of motion points on a user's lower leg is shown; Figure 3 An exemplary embodiment of an electrode array on a user's calf is shown; Figure 4 An exemplary embodiment of the electrode array is shown, wherein the burst pulse sequences for detecting various electrical parameters are represented by dashed lines; Figure 5 The voltage-to-time trace plot shows an exemplary sequence of multiple stimulation pulses and multiple detection burst pulses between electrode pairs; Figure 6 An exemplary embodiment of an electrode array including group electrodes is shown; Figures 7(a), (b) and (c) are voltage-to-time trace plots depicting the skin resistance reduction pulse between electrode pairs, depicted independently and in combination with the stimulation pulse. Figure 8 An exemplary voltage-to-time trace plot is shown, depicting the combination of a sensory blocking pulse and a stimulation pulse; Figure 9 An exemplary method for providing electrical stimulation to a user's muscles using at least one electrical stimulation (ES) system according to this disclosure is shown; Figure 10 A flowchart illustrating an exemplary method for performing detection; and Figure 11 An exemplary embodiment of a computer-readable storage medium is shown. Detailed Implementation

[0037] like Figure 1 As shown in this disclosure, a system 100 including a controller 101 and an electrical stimulation (ES) system 102 is described. The ES system 102 includes an electrode array 104 and one or more sensors 105. In one or more embodiments, the ES system 102 may further include a garment 103. In one or more embodiments, the ES system 102 may include multiple garments 103, wherein each garment includes a corresponding electrode array 104 and one or more sensors 105, or a single garment may include multiple electrode arrays 104 and associated one or more sensors 105. Within a single garment, each electrode array 104 may form an independent ES system 102 with its own controller.

[0038] Controller 101 can be any suitable electronic controller 101 configured to provide and receive signal transmissions to or from ES system 102 or any component of ES system 102. Controller 101 may include at least one processor and at least one memory, the at least one memory including computer program code. The at least one memory and computer program code may be configured, together with the at least one processor, to enable controller 101 to provide signal transmissions to ES system 102. Controller 101 may also be configured to receive signal transmissions from ES system 102 and process the received signal transmissions, such that controller 101 can act on the information included within the signal transmission. The actions that controller 101 may take based on the received signal transmissions will be described in more detail below. It should be understood that controller 101 may use any suitable means to provide and receive signal transmissions. For example, controller 101 may be electrically coupled to ES system 102, such that signals are transmitted directly via physical conduction devices such as wires, conductive rails, conductive fibers, or conductive fabrics. Alternatively, controller 101 may provide signaling to enable a wireless transceiver to transmit and receive signaling to and from ES system 102, and ES system 102 may include corresponding transceivers configured to transmit and receive signaling. In such an example, ES system 102 may include an ES controller (not shown) configured to interpret signaling received from controller 101.

[0039] In some instances, controller 101 may be integrated into one or more garments 103, or may be a remote device, such as a control box mounted on the hip or a computing device (such as a mobile phone, tablet, laptop, or personal computer (PC)) that provides communication with one or more garments 103 of ES system 102.

[0040] In one or more embodiments, controller 101 may include a coordination controller and one or more ES system controllers. In such embodiments, each ES system controller sends and receives signals to control a single ES system 102, and sends signals to and receives signals from the coordination controller. The coordination controller sends high-level control signals to the ES system controllers, which then generate low-level control signals for the ES system 102. For example, the coordination controller may instruct all ES system controllers to switch to detection mode, causing the ES system controllers to begin generating signals to measure detection parameters between electrode pairs in their electrode array 104.

[0041] In one example, a user wears clothing covering their legs, which contains multiple discrete ES systems, each including an ES system controller. One ES system includes an electrode array 104 positioned above the right leg, and another ES system includes an electrode array 104 positioned above the left leg. A coordination controller can be a mobile phone, tablet, or any other mobile device that wirelessly communicates with each of the ES system controllers. The coordination controller performs calculations and determines the operating mode of the ES system 102.

[0042] Electrical stimulation (ES) encompasses a range of techniques involving the application of one or more electrical signals or pulses to stimulate one or more muscles or nerves at a target body part. One such example of ES is neuromuscular electrical stimulation (NMES); however, it should be understood that any suitable ES technique may be used. Other examples of suitable electrical stimulation techniques may include, but are not limited to, electromuscular stimulation (EMS), Russian electrical stimulation, functional electrical stimulation (FES), and transcutaneous electrical nerve stimulation (TENS).

[0043] In one or more instances, the plurality of electrodes of electrode array 104 may be configured to be directly connected to a user via any suitable means. The electrode array may include both stimulating electrodes and detecting electrodes, the stimulating electrodes being configured to provide stimulation of one or both of a muscle and a nerve, and the detecting electrodes being configured to detect electrical parameters indicative of muscle or nerve stimulation. For example, multiple individual electrode pads may be attached to the user, and these electrodes together define the array of electrodes 104. In such embodiments, controller 101 may be connected to the electrodes of electrode array 104 in any suitable manner. In yet another instance, one or more electrodes of electrode array 104 may provide the functionality of both stimulating and detecting electrodes. In other instances, garment 103 may provide support for the relative arrangement of the electrodes of electrode array 104. For example, garment 103 may be clothing, patches, wraps, or adhesive pads configured to be worn by a user.

[0044] It should be understood that in this article, the user is defined as a person or animal to be subjected to electrical stimulation. This does not exclude one or more other people assisting the user, such as a doctor. It could even be that the user is unaware and not operating the system at all, but that someone else (such as a practicing physician) is providing any necessary input to the system.

[0045] In an example where the ES system 102 includes a single garment 103, the system 100 as a whole can be fully integrated into the garment 103 itself, such that the controller 101 includes a microprocessor embedded in the garment 103 along with the electrode array 104 and one or more sensors 105 of the ES system 102. In other examples, the entire system 100 may include multiple garments 103, wherein each of the electrode array 104 and one or more sensors 105 of each garment communicates with the controller 101 for signal transmission. In embodiments where the ES system 102 includes multiple garments 103, the controller 101 may be integrated into one of the garments 103, or it may be integrated into a device remote from any garment 103 of the ES system 102.

[0046] ES technology can be used to prevent several adverse medical conditions (as already discussed) or improve bodily function. Proper application of ES helps reduce the impact and likelihood of these conditions by working through several mechanisms, including: stimulating muscles and thus enabling them to work and become stronger or maintain their current strength; improving arterial circulation by forcing blood to move through the veins; activating the nervous system; releasing growth factors; and releasing anticoagulants. For some users whose blood circulation is below ideal levels, the additional assistance in improving blood flow can be particularly beneficial and helpful.

[0047] Clothing 103 herein refers to an item that can be worn on the body of a person or animal, wherein the person or animal wearing clothing 103 is defined as a user of ES system 102. It should be understood that clothing 103 may include garments such as socks, gloves, tights, boxer shorts, long underwear, vests, or other clothing. Alternatively, clothing 103 may be a bandage, patch, cast, or other medical wrapping or support garment that can be applied to the body of a person or animal for extended periods and during the user's normal activities. Clothing 103 as referred to herein is configured to provide support for the relative arrangement of electrodes of electrode array 104 and one or more sensors 105, in order to distribute the electrodes at least on at least a portion of the user's body. Clothing 103 may be configured to distribute the electrodes of electrode array 104 such that each electrode is in contact with the user's skin, such that applying two different voltages to two different electrodes of electrode array 104 causes stimulation of muscles or their nerve innervation (if present) under the skin. In cases where muscles or their nerve innervation are located under the skin to which electrodes are in electrical communication, the muscles may contract in response to electrical stimulation. Muscle stimulation can be achieved through its innervation, which refers to the electrical stimulation of adjacent or distant nerves connected to the muscle. Muscle stimulation via innervation can be alternatively called indirect muscle stimulation, while direct stimulation of the muscle can be called direct muscle stimulation.

[0048] Figure 2 An example of a human user's leg is shown. Each muscle in the body includes one or more motor points 106. A motor point 106 is defined as a skin area above a muscle or its innervation that requires minimal electrical stimulation to elicit a muscle twitch or contraction. Here, a motor point 106 of a muscle may refer to a point connected to a nerve that, when electrical stimulation is applied thereto, provides muscle contraction via innervation. For example, the calf muscles may include multiple different motor points 106. In the ES device, by accurately targeting the user's motor points 106 as the target of electrical stimulation, power is saved, thereby increasing the lifespan of the system 100 of this disclosure before recharging is required. Furthermore, it has been found that when a motor point 106 is electrically stimulated, user discomfort is reduced compared to stimulating a non-motor point. As defined herein, electrical stimulation at a pair of motor points can also provide increased blood flow to the user by providing stimulation of the muscle. In some instances, the optimal point for stimulation may not be the optimal point for achieving the maximum possible muscle contraction or the minimum possible current required for stimulation. However, since such selected points provide the best desired results, such points will also be referred to herein as motor points. Conversely, placing only a single electrode at the motor point 106 and a second electrode at a non-motor point location may be particularly advantageous for providing ES stimulation via the electrodes closest to the motor point 106. This allows for the identification of optimal point pairs for providing electrical stimulation to induce muscle contraction. This provides points on the body that are most comfortable for the user to stimulate and use minimal energy to induce the desired level of muscle contraction. In some cases, using conventional methods, one or both of these points may not be identified as motor points 106 because conventional methods operate by manually searching for a single point relative to a fixed reference point, such as by using a motor point pen. Instead, system 100 can define motor points by searching for one or more optimal pairs of points using a motor point scanning pattern. That is, motor points, as defined herein, will be those points that provide favorable results with respect to one or more desired stimulation parameters. One or more desired stimulation parameters may include, but are not limited to: maximum muscle contraction; the minimum current required for the desired level of contraction; and maximum induced blood flow. Therefore, the motor points here can be considered as the optimal stimulation points for achieving the desired effect.

[0049] In one or more instances, it is possible that a location on a muscle that is identified as a motion point using conventional motion point recognition techniques (such as by using a motion point pen) may not be identified as a motion point using the methods disclosed herein. In some cases, conventional methods that repeatedly use the same standard reference electrode for each measurement in order to find a single motion point may not offer the same flexibility in identifying optimal location pairs. In fact, in some instances, motion points identified by motion point scanning patterns can select two completely different locations for the motion point compared to conventional methods.

[0050] Figure 3 An example of a user's leg is shown, and an electrode array 104 is arranged thereon. The electrode array 104 includes a plurality of electrodes configured to make electrical contact with the user's skin during use. It should be understood that this may typically mean that the electrodes are in direct physical contact with the user's skin; however, in other embodiments, one or more conductive materials may be disposed between each electrode and the skin during use.

[0051] The electrode array 104 can be arranged in any manner suitable for providing stimulation to multiple different points on the muscle. In one or more embodiments, such as Figure 3 As shown, the electrodes can be arranged in a matrix arrangement. In a matrix arrangement, the electrodes can be arranged in a regular grid pattern to provide full coverage of the target muscle. Each electrode in electrode array 104 can be individually addressable, allowing a voltage to be applied to each electrode while isolated from each other. Each electrode in electrode array 104 can be electrically isolated from each other when not in electrical contact with a conductive medium such as skin, and forms a high resistivity contact between them when in contact with skin. When an electrode does not have a voltage applied to it, due to signal transmission from controller 101, the electrode can be decoupled from any voltage source or ground of ES system 102, such as by turning on a switch. This eliminates any possibility of current flowing between incorrect electrodes. The isolation of each unconnected electrode can be controlled by controller 101. Electrode array 104 can include, for example, more than 10, 20, 50, 100, 225, or any other number of electrodes.

[0052] The controller 101 can provide signaling to the ES system 102 to selectively operate the electrode array 104 in one of a variety of modes, such as detection mode, stimulation mode, motion point scanning mode, or calibration mode. In any of these three modes, a potential difference is applied between at least two distinct electrodes in the electrode array 104. Applying a potential difference between these two electrodes can be configured to directly or indirectly stimulate a muscle at a target body part, where the target body part is the site at the two electrodes or the site between the two electrodes. If alternative parameters are selected, a potential difference can be configured to apply between the two electrodes to avoid stimulating the muscle at the target body part. For example, when operating in detection mode, the controller 101 can be configured to avoid stimulating the muscle at the target body part by selecting appropriate parameters. When operating in motion point scanning mode, the controller 101 can be configured to cause the electrical stimulation system 102 to stimulate the muscle to a lesser degree than in stimulation mode. When operating in stimulation mode, the controller 101 can be configured to cause the electrical stimulation system 102 to stimulate the muscle at the target body part to a greater degree than in motion point scanning mode by applying multiple stimulation pulses.

[0053] Voltages can be applied with opposite polarities; that is, one voltage is positive and the second voltage is negative relative to a reference voltage such as ground. The reference voltage can be considered as a portion of the voltage between two different voltages applied to the first and second electrodes, and therefore, the voltages can be in opposite polarities. It should be understood that the voltage can be measured to have other values ​​relative to another reference voltage, such as 0V and +5V. It should be understood that regardless of the chosen reference voltage, a potential difference exists between the electrodes providing electrical stimulation. Electrodes that do not have a voltage applied to them can be considered essentially at a reference voltage (such as ground voltage) due to the signal transmission provided by controller 101, or these electrodes can be completely disconnected from the circuit. In some instances, voltages applied to the electrodes can be applied simultaneously to generate a potential difference between selected electrodes.

[0054] The controller 101 can provide signal transmission to the ES system 102 to selectively operate the electrode array 104 in a detection mode, where applying a potential difference between electrode pairs can be used to detect body movement. This is accomplished by sending low-intensity electrical pulses across or across the user's body between two electrodes in the electrode array 104. The path taken by the pulses can be characterized by detection parameters. As the body moves, the relative positions between the electrodes can change relative to each other, and the electrodes can also move relative to the body itself (e.g., by sliding on the skin). This changes the path taken by the detection pulses between these electrodes, which in turn changes the value of the detection parameters. Therefore, the change or period of high fluctuation in the detection parameters measured between the two electrodes over time can indicate body movement.

[0055] For example, two electrodes in electrode array 104 can be located on the upper front and lower front of the user's knee, respectively. When the user's leg is straight, the detection pulse between the electrode pairs can primarily cross the user's skin without significantly penetrating into the tissue. When the user's leg is bent, the primary electrical pathway used by the detection pulse can pass more through the muscles or nerves of the user's leg. When the leg is straight, the detection pulse transmitted between the electrode pairs will measure different detection parameter values ​​compared to the pulse passing through a bent leg. Therefore, knee movement can be detected. In other instances, movement of the body physically connected to the electrodes may not change the path of the detection pulse propagation, but the contact resistance between the electrodes and the skin may change with the movement of the body relative to the electrodes.

[0056] The detection mode utilizes the electrodes of electrode array 104, offering several advantages. First, the ES system 102 can be used to provide sensitive and high-resolution motion detection. It has been found that even minute movements and muscle twitches produce changes that can be detected by applying detection pulses to the electrodes. By generating a sequence of electrical parameter detection burst pulses across multiple different electrode combinations, the controller 101 can collect enough data to accurately locate and identify user movements. Furthermore, the same electrode array 104 can be used for both stimulus and motion detection, meaning that expensive additional sensor sets that must be integrated with each other are unnecessary.

[0057] The detection mode can also be used to check whether the electrode array is correctly positioned on the user's body. When the electrodes are not positioned close to the user's skin, there will be no electrical path between the electrodes, and the resistance calculated between any electrode pair will be infinite. Therefore, if infinite resistance is calculated for each electrode pair in the electrode array, the array may not be properly positioned against the user. Similarly, if infinite resistance is calculated for electrode pairs that include electrodes in a specific area of ​​the electrode array, that area of ​​the electrode array may not be correctly positioned against the user's body.

[0058] The detection period is a time interval during which one or more detection parameters indicative of muscle activity can be detected. Generally, the detection period does not overlap with the application of stimulation pulses, as lower-intensity detection pulses may be masked by higher-intensity stimulation pulses between the same or adjacent electrodes. However, in some embodiments, detection may occur between one subset of electrodes in the electrode array 104, while another subset of electrodes is used for stimulation. The detection period also differs from the low-power period, during which the controller 101 and / or ES system 102 can be configured to standby mode. During the detection period, the controller 101 can be configured to receive and record detection parameters from the electrode array 104 to calculate electrical parameters for each electrode pair. Detection parameters and electrical parameters will be discussed further below. The values ​​of the electrical parameters can be calculated simultaneously during the detection period, or alternatively, to reduce computational load, the detection parameters can be recorded and the electrical parameter values ​​calculated after the detection period.

[0059] refer to Figure 4The signal transmission provided by controller 101 during the detection mode causes the ES system to provide multiple electrical parameter detection burst pulse sequences 401 between electrode pairs 402. Each electrical parameter detection burst pulse sequence 401 contains one or more detection pulses. The electrical parameter detection burst pulse sequences 401 can be provided sequentially, such that electrical parameter detection burst pulse sequence 401ab is provided first between electrodes 402a and 402b, followed by electrical parameter detection burst pulse sequence 401ac between electrodes 402a and 402c, and then electrical parameter detection burst pulse sequence 401ad between electrodes 402a and 402d. Controller 101 can also provide electrical parameter detection burst pulse sequences 401 simultaneously. This reduces the time required to run electrical parameter detection burst pulse sequences between all possible electrode pairs. However, it must be noted that the discharges of the simultaneously occurring electrical parameter detection burst pulse sequences 401 must not interfere with each other, as mutual interference may distort the detection parameter measurement results. Therefore, if an electrical parameter detection burst pulse sequence 401 is provided between the first electrode pair located in the same region of array 104, a second electrical parameter detection burst pulse sequence 401 should only be provided simultaneously between the two electrodes located at the far end of that region. For example, an electrical parameter detection burst pulse sequence 401ab between electrodes 402a and 402b can be provided simultaneously with an electrical parameter detection burst pulse sequence 401xy between electrodes 402x and 402y, since electrodes 402a and 402b are both located at the far ends of electrodes 402x and 402y. However, an electrical parameter detection burst pulse sequence 401ab should not be provided simultaneously with an electrical parameter detection burst pulse sequence 401ac between electrodes 402a and 402c, because electrodes 402a, 402b, and 402c are close to each other.

[0060] In addition to the detection pulse, the electrical parameter detection burst pulse sequence 401 may include discrete time intervals for recording the measurement results of the detection parameters or for performing calculations.

[0061] During the detection period, multiple electrical parameter detection burst pulse sequences 401 can be provided between individual electrode pairs. This allows for variations in the detection parameters (and thus the motion) to be detected from a single detection period. However, during a single detection period, electrical parameter detection burst pulse sequences 401 will always be provided between at least two different electrode pairs of the electrode array.

[0062] Figure 5A graph illustrating the relative voltage applied between the electrode pairs is shown, with time plotted along the x-axis and relative voltage plotted along the y-axis. In this example, the electrode array 104 is initially configured to selectively operate in a stimulation mode based on signal transmissions received by the ES system 102 from the controller 101. In the ES system 102, electrical stimulation applied during the stimulation mode can be provided to the user multiple times consecutively to induce muscle contraction and increased blood flow.

[0063] Each stimulation pulse 501 may be applied within the stimulation duration 502a. The stimulation pulses 501 may be applied continuously and uninterruptedly, such that when the first stimulation pulse completes, the subsequent second stimulation pulse begins immediately. In other instances, one or more or each stimulation pulse may be separated by a rest period 502b during which no stimulation pulse 501 is applied. When operating in stimulation mode, a single stimulation cycle 502 may be defined as the period from the beginning of the first stimulation pulse to the beginning of the second stimulation pulse following that first stimulation pulse 501. In instances where there is no rest period 502b between stimulation pulses 501, the duration of the stimulation cycle 502 is equal to the stimulation duration. In instances where a rest period 502b is provided between consecutive stimulation durations 502a, the duration of the stimulation cycle is equal to the stimulation duration 502a plus the duration of the rest period 502b.

[0064] The application of stimulation pulse 501 involves applying a stimulation potential difference between the first and second stimulation electrodes. Each stimulation pulse 501 may be separated by a rest period 502b, during which no stimulation pulse occurs. Therefore, each stimulation pulse 501 can be described as the application of a stimulation signal, wherein each stimulation signal includes applying a first stimulation voltage to the first stimulation electrode and a second stimulation voltage to the second stimulation electrode to provide electrical stimulation to the muscle or its nerve innervation via the skin between the first and second stimulation electrodes. The first stimulation voltage differs from the second stimulation voltage to provide a stimulation potential difference. It should be understood that the amount of stimulation applied to the muscle will vary depending on the user and the desired effect.

[0065] Controller 101 is configured to provide a signal to ES system 102 such that a stimulation signal is applied as a monophasic or biphasic waveform. A biphasic waveform can be generated by applying a voltage VS1 to the first electrode while holding the second electrode at a reference voltage V0 (which can be ground). After applying voltages VS1 and V0, a ​​voltage VS2 is applied to the second electrode while holding the first electrode at the reference voltage V0. The amplitudes of the first stimulation voltage VS1 and the second stimulation voltage VS2 can be the same or they can be different. Controller 101 can be configured to provide a signal to ES system 102 such that the first stimulation voltage VS1 and the second stimulation voltage VS2 are applied as square waves of opposite polarities. This can provide particularly stable and consistent electrical stimulation. Alternatively, the stimulation voltage providing a stimulation potential difference between the electrodes can be provided as a sinusoidal alternating voltage, where each newly applied stimulation signal corresponds to a sine wave passing through a reference voltage, which can be at a relative 0 volt.

[0066] The controller 101 can be configured to apply stimulation signals at a fixed rate, such that the stimulation pulses 501 have a consistent pulse frequency and pulse duration. For example, the rate at which the stimulation signals are applied can be between 1 and 100 Hz. In particular, the rate at which the stimulation signals are applied can be 30-40 Hz, and more particularly, the rate at which the stimulation signals are applied can be 36 Hz. As described above, each stimulation pulse 501 has a stimulation duration 502a and can be separated from adjacent stimulation pulses 501 by rest periods 502b. The stimulation duration 502a is determined by the pulse frequency of the stimulation pulses 501 and the duration of the rest periods 502b used. It should be understood that the pulse frequency (the number of stimulation pulses per second) will be practically equal to the frequency of the number of stimulation cycles 502 (the number of stimulation cycles 502 per second). For example, if the stimulation pulse frequency is 36 Hz and the stimulation signals are separated by a rest period of 27.7 ms, then the stimulation duration 502a will be 0.175 ms. The proportion of the stimulation pulse 501 applied to the stimulation cycle can be referred to as the duty cycle of the signal. In this way, the stimulation pattern can operate with a 50% duty cycle when the stimulation signal is applied for half the duration of the stimulation cycle.

[0067] The controller 101 may be further configured to provide control over one or more other parameters relating to the application of the stimulus signal 501 or the detection of electrical parameters in a burst pulse sequence. For example, the controller 101 may provide control over the duration of a phase and the duration between phases. The controller 101 may provide control over the rise and fall times, where these times correspond to the amounts of time taken to reach the desired first and second voltages, and the amounts of time taken to fall from the first and second voltages, respectively. When neither a rise nor a fall time is set, the controller may also provide control over the plateau time.

[0068] The ES system can operate in detection mode during rest period 502b, allowing the detection period to be defined as the time interval during which multiple electrical parameter detection burst pulse sequences 503 are applied between detection electrode pairs in the electrode array. The detection electrodes can be the same as the stimulation electrodes or different electrodes. The minimum duration of the detection period can be determined by the speed of the processor used by the controller and the number of electrodes in the electrode array 104 used for detection. The detection period is related to the controller's processor speed because no treatment or other effects are required when applying the electrical parameter detection burst pulse sequence to the user. Instead, only electrical parameter measurements, such as resistance measurements between the two detection electrodes, are needed. In one example, the minimum duration of the detection period, expressed in seconds, would be equal to (1 / (processor frequency / 2))×((N(N-1)) / 2), where N is the number of detection electrodes in the electrode array 104. If the electrode array 104 has 64 electrodes for detection and the processor frequency is 480MHz, a detection period of 8.4 microseconds would be required to transmit detection pulses between all possible electrode pairs. The longest duration of the detection period can be the same as the duration of the rest period 502b, so that the detection period can be alternated with the stimulation pulse 501.

[0069] Each electrical parameter detection burst pulse sequence 504 contains one or more detection pulses 503. Figure 5 The example shown illustrates that each electrical parameter detection burst pulse sequence 504 contains only a single detection pulse 503. In other examples, each electrical parameter detection burst pulse sequence 504 may contain multiple detection pulses 503, such that each electrical parameter detection burst pulse sequence is a wave packet of detection pulse 503. The duration of the detection pulse is generally determined by the processing speed of the controller 101, where the pulse duration 504a is the shortest possible time in which the controller can generate the detection pulse 503. The electrical parameter detection burst pulse sequences 504 may be separated by intervals 504b between burst pulse sequences. For example, if the controller 101 is capable of generating an electrical parameter detection burst pulse sequence 503 containing a single detection pulse with a pulse duration of 1 ms, the pulse frequency would be 1000 Hz without intervals between burst pulse sequences. By providing extended intervals between burst pulse sequences, or by providing intervals between pulses in a single electrical parameter detection burst pulse sequence, detection pulses can be provided at a lower frequency, but each pulse has the same duration. For example, two electrical parameter detection burst pulse sequences can be generated, each containing a single detection pulse with a duration of 1 ms, wherein the interval between the burst pulse sequences has a duration of 98 ms. Generally, the detection pulse frequency can be between 10 Hz and 100 MHz.

[0070] Similar to the stimulation pulse 501, the detection pulse can consist of a biphasic square wave with a maximum potential difference VD1 and a minimum potential difference VD2. Each electrical parameter detection burst pulse sequence 504 is configured not to provide muscle stimulation (activate the muscle, causing the muscle fibers to "twitch"). That is, each electrical parameter detection burst pulse sequence is configured to set at least one or more of the signal amplitude, frequency, and / or waveform to a level such that the detection pulse is insufficient to induce muscle activation at the target body site. Specifically, at least one or more of the signal amplitude, frequency, and waveform can be selected such that they are insufficient to induce muscle stimulation at the target body site. That is, stimulation is avoided by selecting appropriate waveform parameters. Specifically, the electrical parameter burst pulse sequences are configured such that when they are delivered independently, they do not provide stimulation that induces muscle activation at the target site. Figure 5 In this process, the absolute potential difference |VD1-VD2| of the detection pulse 503 is less than the absolute potential difference |VS1-VS2| of the stimulation pulse 501, so that the detection pulse 503 does not induce muscle activation. For example, one parameter to avoid muscle stimulation could be to maintain the current supplied between each pair of detection electrodes at no more than 0.1 mA during each detection pulse 503.

[0071] In an alternative example, calibration can be performed for each patient to determine the intensity of the stimulus 501 and the detection pulse 503. For example, starting with a low intensity (equal to or below the minimum expected intensity to elicit stimulation), pulses of gradually increasing intensity can be applied to the user until muscle activation is observed at a certain threshold intensity. The stimulus pulse 501 is then set to have an intensity equal to or above that threshold, while the detection pulse 503 is set to have an intensity below that threshold.

[0072] The electrical parameter detection burst pulse sequence 504 may be intentionally provided simultaneously with another signal (such as a stimulation signal), and this other signal may be provided alone or in combination with the electrical parameter detection burst pulse sequence to provide stimulation of nerves or muscles at a target body part. Such embodiments will still fall within the scope of this disclosure. In other instances, the electrical parameter detection burst pulse sequence 504 and the stimulation pulse 501 may be provided independently.

[0073] Alternating stimulation pulses 501 and electrical parameter detection burst pulse sequences 504 can be used to calculate changes in electrical parameter values ​​in response to stimulation. For example... Figure 5For clarity, a delay may exist between the end of stimulation pulse 501 and the start of the detection period. Alternatively, the detection period may begin immediately after the stimulation pulse ends. In one or more embodiments, electrical parameters may be calculated multiple times during the detection period to monitor changes in electrical parameters during the detection period. For example, electrical parameters may be calculated based on a first electrical parameter detection burst sequence 503, and then recalculated based on subsequent electrical parameter detection burst sequences. This allows for the detection of changes in electrical parameters between electrode pairs.

[0074] As shown in the figure, the stimulation pulse 501 and each detection pulse 503 of the electrical parameter detection burst pulse sequence 504 are biphasic square waves. However, alternatively, either or both of the stimulation pulse and detection pulses can be monophasic pulses. In other instances, the stimulation pulse and detection pulse can comprise monophasic or biphasic sine waves, sawtooth waves, or another waveform shape.

[0075] The controller 101 is further configured to detect one or more detection parameters that indicate the degree of bodily activity associated with each electrical parameter detection burst pulse sequence. That is, the controller can receive signal transmissions from the detection electrodes indicating at least one of resistivity, resistance, conductivity, conductance, impedance, and admittance. The listed electrical parameters can indicate the degree of bodily activity relative to the detection pulse, as any of these parameters will provide an indication of the charge transferred through the body. For example, the resistance of the charge transferred through the body during the detection pulse (the current through the body) depends on several factors, including at least transcutaneous, transsubcutaneous, or transmuscular resistance and the contact resistance between the electrodes and the body. By obtaining a measurement of the resistance, an indication of changes in contact resistance can be obtained, and in this way, it can be determined whether the muscle is currently or has been in motion. In this example, the detection parameter can be the current passing through a nerve, muscle, or any other tissue in an electrical pathway located between the detection electrodes.

[0076] If the electrode array 104 is in electrical contact with the controller 101, the provision of a signal (which may be referred to as a measurement result signal transmission) can be performed simply by providing the controller 101 with a voltage indicating the measurement result. In other embodiments, the measurement result signal transmission may include, for example, a wireless signal sent from the ES system controller to the controller 101.

[0077] The controller 101 is further configured to calculate electrical parameter values ​​between each pair of detection electrodes based on one or more detection parameter values. For example, the controller may be configured to calculate the resistance (electrical parameter) between the two detection electrodes based on a current (detection parameter) flowing through an electrical pathway located between the detection electrodes in a muscle, nerve, or any other tissue, which is generated by a potential difference applied between the two electrodes of the detection electrode pair.

[0078] As defined herein, an electrode pair refers to a combination of a first detection electrode and a second detection electrode. During a given detection period, at least one subsequent electrical parameter detection burst pulse sequence is not provided between the same two detection electrode combinations, but rather between different combinations of two electrodes in the array. For example, if a potential difference is applied between electrode A and electrode B to provide a first electrical parameter detection burst pulse sequence, then at least one subsequent electrical parameter detection burst pulse sequence among multiple electrical parameter detection burst pulse sequences will not use electrodes A and B during the same given detection period, but rather use electrodes A and C, electrodes B and C, or electrodes C and D during the same given detection period. This specification does not entirely limit the performance of repeated measurements, but multiple measurements are performed on different electrode pairs to provide electrical parameter detection burst pulse sequences that effectively determine the electrical parameters for multiple electrode pairs.

[0079] In one or more embodiments, the electrode array 104 can be operated in a detection mode such that, within a single detection period, all electrode pair combinations in the electrode array 104 apply a potential difference thereon as a separate measurement. The controller can be configured to iterate through all possible electrode pairs by selecting a first electrode and then sequentially sending a sequence of electrical parameter detection burst pulses between that electrode and each of the other electrodes in the array 104. The controller then selects a second electrode and sends a sequence of electrical parameter detection burst pulses between the second electrode and each of the other electrodes in the array 104 besides the first electrode. This process is repeated until the sequence of electrical parameter detection burst pulses has been passed between all possible electrode pairs in the array. In other instances, the order in which the electrode pairs are selected can be based on a different sorting, or the order can be randomized.

[0080] By providing measurements between each definable pair of electrodes in the electrode array, the maximum possible number of sensors during a detection mode can be provided, thereby providing the maximum possible measurement resolution through this technique. In one or more embodiments, the controller 101 can be configured to provide signaling to the ES system to provide a sequence of electrical parameter detection bursts between at least 50% of the definable detection electrode pairs within the electrode array, and correspondingly detect one or more detection parameters indicating electrical parameters that themselves indicate the degree of bodily activity. Alternatively, the percentage of possible activated electrode pairs can be at least 30%, at least 40%, at least 60%, at least 70%, at least 80%, or at least 90%. By acquiring a large number of measurements between different electrode pairs definable within the array, a corresponding number of sensors can be effectively created, which can provide improved accuracy, reliability, and position specificity compared to, for example, using a small number of flexible sensors.

[0081] Maximum resolution in detection mode can be achieved by providing a burst pulse sequence for electrical parameter detection between all possible electrode pairs. For an electrode array 104 containing a total of N electrodes, the number of possible electrode pairs is given by the binomial coefficient C(N,2), which is equal to N! / (2!(N-2)!) =(N-1)(N / 2). For example, in a 2×2 array, 6 unique electrode pairs can be defined. As the number of electrodes in the electrode array 104 increases, the number of combinations of electrode pairs increases rapidly. For example, in an electrode array 104 containing 10 electrodes, there are 45 possible electrode pairs; in an electrode array 104 containing 100 electrodes, there are 4950 possible electrode pairs; and in an electrode array 104 containing 150 electrodes, there are 11175 possible electrode pairs. Therefore, in an electrode array 104 larger than a certain size, providing a burst pulse sequence for electrical parameter detection between all possible electrode pairs may become impractical. Instead, a burst pulse sequence for electrical parameter detection can be sent between groups of electrodes or between subsets of possible electrode pairs.

[0082] Electrode array 104 can be divided into a first subarray and a second subarray, each subarray corresponding to a different part of the muscle to which the electrodes of the electrode array are intended to contact. In these embodiments, each electrode of the first subarray forms an electrode pair with each electrode of the second subarray, such that each electrode pair includes one electrode from each subarray. This avoids testing electrode pairs intended to be associated with the same point of motion 106, thereby providing sensors that are more spaced apart from each other, which, for example, can yield more reliable measurements of muscle movement.

[0083] The signal transmission from controller 101 enables the ES system to operate in detection mode, providing the ability to efficiently create a large number of sensors distributed throughout the body, to which the electrode array is attached, without adding additional components that occupy both space and consume power. This allows for a more compact and comfortable ES system for the user, which in turn leads to continuously improving user compliance.

[0084] Figure 6An exemplary electrode array 104 is shown defining a 4×4 group of electrodes 601, a 2×2 group of electrodes 602, and a motion point 106. The electrode array 104 can be configured such that multiple individual electrodes can be voltaged simultaneously to define larger group electrodes 601, 602. The voltages applied to the group electrodes 601, 602 can be substantially the same. The electrical contact of the electrodes allows for the simulation of a single large electrode, and the electrodes can be defined in any shape suitable for stimulating a motion point. Such group electrodes can be used as either stimulation electrodes or detection electrodes. In one or more instances, instead of defining electrode lines, the group electrodes can be substantially point-like. For example, group electrodes 601, 602 can be defined by a substantially square or circular grid, such as the 4×4 grid of electrode 601 in the regular matrix electrode array 104. One or more group electrodes 601, 602 can be used to improve the efficiency of detecting the response of muscles or nerves to electrical stimulation, or they can be used to provide stimulation to a larger area of ​​the body during stimulation patterns. Alternatively or additionally, one or more group electrodes 601, 602 may be used to detect the activity of muscles associated with the group electrodes without eliciting stimulation. In the case of certain muscle groups, the group electrodes may provide improved muscle stimulation by using multiple individual electrodes to provide stimulation of a single motor point 106.

[0085] Using group electrodes offers several advantages. Searching for all electrode combinations in array 104 is a time-consuming process, becoming increasingly difficult as the number of electrodes in array 104 increases. Using group electrodes can significantly reduce total measurement and processing time while providing sufficiently high resolution to detect muscle movements induced by muscle stimulation.

[0086] Group electrode detection can also be used as part of the algorithm's search pattern to detect and locate motion more efficiently. For example, electrode array 104 can be divided into large-scale group electrodes. An initial set of electrical parameter detection burst pulse sequences is provided between the group electrodes, and calculated electrical parameters are used to indicate the level of motion associated with each group electrode. Group electrodes with high motion levels are further divided into smaller group electrodes, and electrical parameter detection burst pulse sequences are provided between these smaller group electrodes. This process continues until the controller has located the individual or group electrodes associated with the high motion level, thereby identifying the location of the motion. This approach may be more efficient than simply sending electrical parameter detection burst pulse sequences between every possible combination of electrode pairs.

[0087] Instead of using a single electrode to provide stimulation to the motor point 106 during stimulation mode, some muscles can be better stimulated by providing stimulation over an area larger than a single electrode. Therefore, controller 101 can be configured to identify a first stimulation group electrode and a second stimulation group electrode, wherein each group electrode is aligned with a different motor point 106 of the user's muscle. Controller 101 can then be configured to provide a signal to cause ES system 102 to operate electrode array 104 in a group electrode stimulation mode, wherein this signal results in multiple stimulation signals being applied to the first and second stimulation group electrodes. Each stimulation signal may include applying a first stimulation voltage to the first stimulation group electrode and a second stimulation voltage to the second stimulation group electrode to provide electrical stimulation to the muscle or its nerve innervation via the skin between the electrode pairs, and wherein the first stimulation voltage has a different polarity than the second stimulation voltage. It should be understood that the group electrode stimulation mode is directly similar to the stimulation modes previously described, except that the electrodes are actually larger. Similarly, a group electrode detection mode can be provided.

[0088] To prevent problems caused by user inactivity, controller 101 can be configured to detect user inactivity, and if the user has been inactive for a predetermined period of time, controller 101 can be configured to at least activate a stimulation mode. Specifically, controller 101 can also be configured to cause ES system 102 to operate in a detection mode, even if the ES system has not recently been operating in stimulation mode. This detection mode may be referred to as a passive detection mode; however, it operates in the same manner as the detection mode already described (which may be referred to as an active detection mode). During detection mode, controller 101 is configured not to provide signal transmission to allow ES system 102 to apply voltage at any electrode at a level sufficient to stimulate one or both of the muscles and nerves. During detection mode, controller 101 is further configured to continuously or periodically receive signal transmissions from ES system 102 indicating detection parameters. It should be understood that continuous or periodic monitoring of user activity provides valuable information about user activity. ES system 102 can default to operating in this detection mode when it is not operating in other modes.

[0089] User-induced stimulation refers to muscle contraction resulting from the user's intentional use of the muscle in question. If the controller 101 determines, based on signal transmission received during the detection period, that the contraction is within a predetermined threshold of the calibration signal transmission, then the movement can be considered solely as user-induced stimulation. The calibration signal transmission is a signal indicating the user's muscle contraction during calibration mode. That is, a small amount of user movement (below the muscle response threshold or the threshold of the calibration signal transmission) may not be sufficient to stimulate the desired blood flow or muscle exercise. In such cases, it may be desirable to operate the ES system 102 in stimulation mode.

[0090] If controller 101 does not receive indication of user-induced stimulation during the detection period of passive detection mode, controller 101 may be configured to cause ES system 102 to operate in an alternative mode (such as stimulation mode). Other alternative modes may include a calibration mode for determining baseline electrical parameter values ​​or a motion point scanning mode configured to identify preferred motion points for stimulation. The detection period during passive detection mode may be, for example, 30 minutes, 1 hour, 2 hours, 3 hours, or any other suitable time based on user needs. Controller 101 may be further configured to cause ES system 102 to operate in detection mode during or after the system is operating in stimulation mode.

[0091] In some instances, recorded muscle contractions below a predetermined threshold for calibrating signal transmission within a predetermined upper limit of the contraction duration can be recorded as user-induced stimulation, as this can indicate minimal exercise within an extended time period sufficient to eliminate the need for additional stimulation of the electrode array 104. That is, minimal (below the threshold) movement by the user within the extended time period can be considered acceptable to induce desired blood flow, exercise, or other stimulating effects on the user, making stimulation of the ES system 102 unnecessary.

[0092] The controller can be configured to generate an electrical parameter map representing the spatial distribution of the electrodes in an electrode array. This electrical parameter map includes multiple elements arranged in a grid, and each element includes an element value based on one or more electrical parameters calculated by the controller 101. In other words, the electrical parameter map is a two-dimensional numerical representation of the two-dimensional surface of the electrode array based on electrical parameters calculated between electrode pairs. The grid layout of the electrical parameter map facilitates the detection of patterns in the element values, thereby identifying specific types and locations of motion. The electrical parameter map can be readily stored in the form of a matrix or array on a computer-readable storage medium, allowing for comparison of instances of electrical parameter maps calculated based on different electrical parameter detection burst pulse sequences.

[0093] In one embodiment, each element of the electrical parameter graph corresponds to an electrode of the electrode array, and the element value of the electrical parameter graph is based on the sum or average of the electrical parameters calculated using the corresponding electrode. For example, the value of an element in the first row and first column of the electrical parameter graph may correspond to an electrode in the first row and first column of the electrode array 104. The value of that element may then be set to the sum of the resistance values ​​(resistance being an exemplary electrical parameter) calculated between that electrode and each other electrode in the electrode array 104.

[0094] It should be understood that there may not be a one-to-one correlation between each element in the electrical parameter diagram and each electrode in the electrode array. For example, to reduce the size of the electrical parameter diagram or improve robustness, each element of the electrical parameter diagram may correspond to an electrode cluster. In this way, a 4×4 electrode array 104 can be represented by a 2×2 electrical parameter diagram. Conversely, in some other embodiments, the spatial extent represented by each element may be smaller than that of a single electrode; therefore, the spatial extent of each electrode may be represented by multiple elements.

[0095] The electrical parameter diagram described above makes it easy to identify the location of a specific movement. For example, if a user's movement causes a slight change in the position of an electrode relative to the user's skin, the path between that electrode and each other will change over time. The change in resistance between that electrode and the other electrodes will be greater than the change in resistance between electrode pairs that have not changed position. Therefore, a large change in the value of an element in the electrical parameter diagram can indicate that localized user movement has occurred near the electrode represented by that element. Similarly, large changes in the values ​​of multiple elements representing electrodes in a specific region of the electrode array 104 can indicate user movement throughout the entire area covered by that region of the electrode array.

[0096] To track changes in element values ​​stored in an electrical parameter graph, controller 101 can be configured to calculate the electrical parameter graph based on electrical parameters measured during the current detection period, wherein the element values ​​of the electrical parameter graph are based on the difference between element values ​​calculated during the current detection period and element values ​​calculated during a previous detection period acquired at a time earlier than the current detection period. In other words, each element in the electrical parameter graph represents a difference or increment (Δ) between electrical parameters measured over a time interval. Therefore, a larger absolute value of any element compared to the previous detection period indicates that the user is moving around the electrode represented by that element. The previous detection period can be the most recent detection period acquired compared to the current detection period. That is, the previous detection period can be a detection period preceding the current detection period, which can be: immediately preceding the current detection period; separated from the current detection period by a time delay; or separated from the current detection period by one or more stimulus durations during which a stimulus pulse is applied to the user.

[0097] Instead of comparing electrical parameter values ​​from the current detection period to those from the previous detection period, electrical parameter values ​​can be compared to predefined element values. Predefined baseline electrical parameters can be, for example, electrical parameters obtained during calibration measurements acquired at a previous point in time during calibration mode. Alternatively, baseline electrical parameters can be standardized values ​​not based on measurements acquired by the electrical stimulation system, with comparisons made to these standardized values ​​to detect anomalous deviations.

[0098] The controller 101 can generate an electrical parameter graph, where each element of the graph corresponds to an electrode pair of the electrode array. The value of each element of the electrical parameter graph can be a value of an electrical parameter calculated for the corresponding electrode pair. As described above, the element values ​​of the electrical parameters can be based on the difference between the electrical parameters calculated between the electrode pairs during an electrical parameter detection burst pulse sequence and those calculated between the electrode pairs during a previous electrical parameter detection burst pulse sequence. One element of the electrical parameter graph can correspond to multiple pairs, and the value of that element is calculated as the sum or average of the electrical parameters between each of the corresponding electrode pairs. This allows for the identification of different types of motion. For example, one element of the electrical parameter graph can correspond to electrode pairs separated by a short distance, while another element corresponds to electrode pairs spaced further apart. Motions that cause changes in transmuscular resistance but not transcutaneous resistance (such as slight muscle twitching) will result in a larger change in the value of the second element than the first element.

[0099] Controller 101 can be configured to determine whether to provide a signal to the ES system to operate the electrode array in detection mode or an alternative mode (such as stimulation mode) based on an electrical parameter graph. It should be understood that the values ​​in the electrical parameter graph will indicate changes in electrical parameters over time and with the spatial distribution represented by the graph. Movement of the body part to which the electrodes are coupled will cause changes in the element values ​​of the electrical parameter graph. Therefore, the controller can use the element values ​​in the electrical parameter graph as an indicator of whether the user of the system has engaged in physical activity within a specific time period (such as the time between the previous detection period and the current detection period). As mentioned above, element values ​​can be defined in various ways, such as: the difference between a previous value and a current value or a predefined value; the ratio between a previous value and a current value or a predefined value; the sum of a previous value and a current value or a predefined value; or many other ways of defining element values. Therefore, correspondingly, there are multiple ways to define element values ​​indicating that the user has not moved. For example, the controller can be configured to provide a signal to the electrical stimulation system to operate the electrode array in detection mode or stimulation mode based on one or more element values ​​being higher or lower than a predetermined threshold. Alternatively, the controller can be configured to detect whether the change in element value is greater than or less than a predetermined threshold change. In yet another instance, the controller 101 can be configured to provide a signal to the ES system 102 to operate the electrode array 104 in detection mode or stimulation mode if a predetermined number of consecutive element value changes are greater than or less than a predetermined threshold.

[0100] It has been found that skin resistance and impedance decrease with increasing applied electrical signal frequency. If stimulation pulses are applied at relatively low frequencies (tens of hertz), skin resistance will be high (hundreds to thousands of ohms). This high resistance leads to high local energy dissipation, increasing user discomfort and placing a higher energy demand on the ES system 102. This can be mitigated by applying skin resistance-reducing pulses in stimulation mode, where the skin resistance-reducing pulses are applied at a higher frequency and lower intensity than the stimulation pulses. Unbound by theory, it is believed that the skin resistance-reducing pulses reorient ions in the user's skin, thereby increasing skin conductivity and reducing energy dissipation.

[0101] Turning to Figure 7, the controller can be configured to cause the ES system to apply multiple skin resistance reduction pulses 702 when operating in stimulation mode. Figure 7(a) shows a representation of the skin resistance reduction pulse 702 as a voltage-to-time plot, without any stimulation pulses. The skin resistance reduction pulse 702 is generated by generating an additional potential difference VR1 at one stimulation electrode relative to the voltage V0 of the other stimulation electrode, then holding the first electrode at V0 while holding the other electrode at voltage VR2. The intensity of the skin resistance reduction pulse 702 is lower than that of the stimulation pulse (i.e., the voltage amplitude of the skin resistance reduction pulse 702 is |VR2-VR1| lower than that of the stimulation pulse), but it is applied at a higher frequency than the stimulation pulse. The skin resistance reduction pulse 702 is applied in a skin resistance reduction burst pulse sequence 701. The skin resistance reduction pulse 702 is a biphasic square wave, but can alternatively be a monophasic or biphasic sine wave, a sawtooth wave, or another waveform shape.

[0102] As shown in Figure 7(b), skin resistance reduction pulses 702 can be superimposed on stimulation pulses 501. It should be understood that this will produce constructive interference providing combined waveforms containing high-frequency repetitive waveforms at lower frequencies and higher amplitudes. The skin resistance reduction burst pulse sequence 701b overlaps with and precedes the stimulation duration 502a of stimulation pulse 501. In contrast to the burst pulse sequence 701b, the skin resistance reduction pulses 702 can be continuous when the ES system is operating in stimulation mode.

[0103] In one or more embodiments, each skin resistance reducing pulse 702 may carry a current of no more than 0.1 mA and has a frequency between 1 Hz and 100,000 Hz. This ensures that the skin resistance reducing pulse has a sufficiently high frequency to significantly reduce skin resistance to the stimulation pulse 501 without significantly affecting the intensity of the stimulation pulse 501.

[0104] As shown in Figure 7(c), instead of stacking skin resistance reduction pulses 702 to overlap with the stimulation duration 502a of stimulation pulses 501, the controller can be alternatively configured to synchronize skin resistance reduction pulses 702 such that they do not overlap with stimulation pulses 501. That is, a skin resistance reduction burst pulse sequence 701c is applied during the intervals between stimulation pulses 501.

[0105] Figure 8 A sensory blocking pulse 801 is shown, which is synchronized with the stimulation pulse 501 in the same manner as the skin resistance decreasing pulse 702 in FIG. 7(b). The sensory blocking pulse 801 may also be superimposed on either or both of the stimulation pulse 501 or the skin resistance decreasing pulse 702.

[0106] When stimulation pulse 501 is applied, sensory blocking pulse 801 causes the user to experience less discomfort. When stimulation pulse 501 is applied, high-intensity signals are generated in the user's sensory nerves. These signals are then transmitted via the spinal cord to the brain, where they are perceived as pain. Sensory blocking pulse 801 induces the opposite generation of low-intensity neural signals, blocking the transmission of high-intensity pain signals to the brain via sensory nerves at the spinal cord level when stimulation pulse 501 is applied. In this sense, sensory blocking pulse 801 works in a manner similar to rubbing an area of ​​the body after a minor injury, such as a bruise or abrasion. The sensation of friction "stops" the pain caused by the injury, so the individual feels less pain. Sensory blocking pulse 801 can be applied by multiple electrode pairs surrounding the electrode pairs used for stimulation. For example, sensory blocking pulse 801 can be applied by a group of electrodes surrounding the stimulation electrodes, thereby generating low-intensity blocking signals over a large area of ​​skin that block pain signals.

[0107] The intensity of the sensory blocking pulse 801 is generally lower than that of the stimulation pulse 501, but generally has a higher intensity and a lower frequency compared to the skin resistance-lowering pulse. In one example, the sensory blocking pulse 801 is applied at a pulse frequency between 0.1 Hz and 150 Hz. In this example, the current carried by the sensory blocking pulse 801 is 1 mA to 10 mA lower than that carried by the stimulation pulse 501. In another example, the current carried by the sensory blocking pulse 801 is calibrated for the user. The sensory blocking pulse 801 is initially applied to the user at a current of 0.1 mA or higher, and then the current is increased until the user begins to experience pain relief due to the sensory blocking effect.

[0108] refer to Figure 9A method 900 for providing ES to a user's muscles using the previously described system 100 will now be described. The method includes the steps of: providing a signal transmission 901 to the ES system via a controller to operate an electrode array in a detection mode during a detection period, the signal transmission causing the ES system to provide a plurality of electrical parameter detection burst pulse sequences during at least one detection period, wherein each electrical parameter detection burst pulse sequence includes one or more detection pulses, and wherein each electrical parameter detection burst pulse sequence is configured not to provide muscle stimulation. The method further includes detecting 902 one or more detection parameters via the controller, these parameters indicating the degree of bodily activity associated with each electrical parameter detection burst pulse sequence. Each electrical parameter detection burst pulse sequence is provided by applying a potential difference between different pairs of multiple electrodes. An electrode pair refers to a combination of a first detection electrode and a second detection electrode selected from any electrode of the electrode array, such that when the controller provides a subsequent electrical parameter detection burst pulse sequence, the corresponding electrode pair for that subsequent electrical parameter detection burst pulse sequence includes any pair of two electrodes of the electrode array, except for any electrode pairs corresponding to previously provided electrical parameter detection burst pulse sequences in the detection mode. It should be understood that the discussion regarding avoiding the use of the same two electrodes in an electrode array refers to repeated use during a given rest period or a single operation in detection mode. The method further includes calculating the electrical parameters between each pair of detection electrodes 903 by a controller based on one or more detection parameters.

[0109] Figure 10 A more detailed exemplary embodiment of a method for providing electrical stimulation to a user's muscles is shown. The system is initially configured 1001 to an alternative mode, such as a standby mode. The controller 101 then provides a signaling transmission to the ES system 102 to cause the electrode array 104 to operate in detection mode 1002 during a detection period. The controller 101 may be triggered into the detection period by a timer, for example, entering the detection period after 30 minutes in standby mode.

[0110] When operating in detection mode, controller 101 selects 1003 a first electrode pair from electrode array 104. The controller then provides signaling to cause ES system 102 to provide 1004 a plurality of electrical parameter detection burst pulse sequences during at least one detection period, wherein each electrical parameter detection burst pulse sequence contains one or more detection pulses, and wherein each electrical parameter detection burst pulse sequence is configured not to provide stimulation to one or both of the muscles and nerves at the target body part. Controller 101 detects and measures 1005 one or more detection parameters indicating the body's response associated with each electrical parameter detection burst pulse sequence. The controller then calculates 1006 one or more electrical parameters based on one or more measured detection parameters.

[0111] Following (or simultaneously with) the detection of the burst pulse sequence of electrical parameters, controller 101 selects a second electrode pair, which can be any electrode pair in electrode array 104 other than the previously selected pair, and then repeats steps 1004, 1005, and 1006. Once controller 101 has evaluated 1007 that all the required electrical parameters have been calculated, it can then analyze 1008 the electrical parameters to identify movement. High levels of change in electrical parameters over time indicate movement, while low levels of change indicate a lack of activity.

[0112] If movement is detected, controller 101 can configure system 100 to enter standby mode and start a timer to count down to the next detection period. If no movement is detected, controller 100 can configure system 100 to an alternative mode, such as stimulation mode. In stimulation mode, the controller provides signaling to cause the ES system to provide multiple stimulation pulses separated by rest periods, wherein: each stimulation pulse includes applying a stimulation potential difference between a first stimulation electrode and a second stimulation electrode in the electrode array, such that the stimulation potential difference is configured to provide stimulation at the target body part; and each rest period includes a period of time during which no stimulation pulse is present.

[0113] Figure 11 A computer-readable medium comprising computer program code configured to cause a controller, including a processor and memory, to operate as described herein is shown.

Claims

1. A controller for providing and receiving signal transmissions to at least one electrical stimulation (ES) system, the ES system comprising an electrode array including a plurality of electrodes for applying electrical stimulation to a user's muscles, wherein the electrodes are further configured to measure electrical parameters between any one electrode of the electrode array and any other electrode of the electrode array, wherein the controller is configured to: A signal is provided to the ES system to operate the electrode array in detection mode during the detection period, the signal causing the ES system to provide a plurality of electrical parameter detection burst pulse sequences, wherein each electrical parameter detection burst pulse sequence includes one or more detection pulses, and each electrical parameter detection burst pulse sequence is configured not to provide muscle stimulation; and The detection indicates one or more detection parameters that correlate muscle activity with each electrical parameter detection burst pulse sequence. Each electrical parameter detection burst pulse sequence is provided by applying a potential difference between different pairs of the plurality of electrodes, wherein an electrode pair refers to a combination of a first detection electrode and a second detection electrode selected from any electrode of the electrode array, such that when the controller provides a subsequent electrical parameter detection burst pulse sequence, the corresponding electrode pair for the subsequent electrical parameter detection burst pulse sequence includes any pair of two electrodes of the electrode array, except for any electrode pair corresponding to a previously provided electrical parameter detection burst pulse sequence of the detection period. The controller is configured to calculate the electrical parameters between each pair of detection electrodes based on the one or more detection parameters.

2. The controller of claim 1, wherein the controller is configured to provide a signal to the ES system to operate the electrode array in a stimulation mode, the signal causing the ES system to provide a plurality of stimulation pulses spaced apart by rest periods, wherein: Each stimulation pulse includes applying a stimulation potential difference between a first stimulation electrode and a second stimulation electrode in the electrode array, such that the stimulation potential difference is configured to provide stimulation to the muscle; and Each rest period includes a time when there are no stimulating pulses.

3. The controller of claim 2, wherein the detection period occurs during the rest period, such that one or more detection parameters are measured between the application of stimulation pulses.

4. The controller according to any of the preceding claims, wherein the controller is configured to provide signal transmission to the ES system such that the ES system provides an electrical parameter detection burst pulse sequence between at least 50% of the definable detection electrode pairs within the electrode array, and correspondingly detects one or more detection parameters indicating the degree of bodily activity associated with each electrical parameter detection burst pulse sequence.

5. The controller according to any of the preceding claims, wherein the controller is further configured to determine, based on the electrical parameters calculated between each pair of detection electrodes, whether to provide a signal to the ES system to cause the electrode array to operate in the detection mode or an alternative mode.

6. The controller of claim 1, wherein the detection parameter is a corresponding electrical parameter for detecting the current between electrode pairs during a burst pulse sequence.

7. The controller according to any of the preceding claims, wherein the calculated electrical parameters are at least one of the following: resistivity; resistance; Electrical conductivity; Electrical conductivity; Electrical impedance; and Electrical admittance.

8. The controller according to any of the preceding claims, wherein the controller is further configured to generate an electrical parameter map representing the spatial distribution of the electrodes of the electrode array, wherein the electrical parameter map includes a plurality of elements arranged in a grid, and wherein each element includes an element value based on one or more electrical parameters calculated by the controller.

9. The controller of claim 8, wherein each element of the electrical parameter diagram corresponds to an electrode of the electrode array, and the element value of the element of the electrical parameter diagram is based on the sum of the electrical parameters calculated using each corresponding electrode.

10. The controller of claim 8, wherein each element of the electrical parameter diagram corresponds to an electrode of the electrode array, and the element value of the element of the electrical parameter diagram is based on the average value of the electrical parameter calculated using each corresponding electrode.

11. The controller according to any one of claims 8 to 10, wherein the controller is configured to obtain an electrical parameter map of the electrodes of the electrode array obtained during a current detection period, and wherein the element values ​​of the electrical parameter map are based on the difference between element values ​​calculated during the current detection period and one of the following: The element values ​​calculated during the previous detection period, obtained at a time earlier than the current detection period; and Predefined element values.

12. The controller of claim 8, wherein each element of the electrical parameter graph corresponds to an electrode pair of the electrode array, and the element value of the element of the electrical parameter is based on the difference between the electrical parameter calculated between the electrode pair during the electrical parameter detection burst pulse sequence and the electrical parameter calculated between the electrode pair during a previous electrical parameter detection burst pulse sequence.

13. The controller according to any one of claims 8 to 11, wherein the controller is further configured to determine, based on the electrical parameter diagram, whether to provide signal transmission to the ES system to cause the electrode array to operate in the detection mode or in an alternative mode.

14. The controller according to any of the preceding claims, wherein the electrical parameter detection burst pulse sequence comprises a plurality of detection pulses, each detection pulse having a pulse frequency between 10 Hz and 100 MHz.

15. The controller according to claims 2 to 14, wherein the current provided between each pair of detection electrodes for detecting parameters does not exceed 0.1 mA.

16. The controller of claim 2, wherein the controller is configured to cause the ES system to apply a plurality of skin resistance-reducing pulses during the stimulation period, wherein the skin resistance-reducing pulses comprise a higher frequency and a lower intensity compared to the plurality of stimulation pulses.

17. The controller of claim 16, wherein the plurality of skin resistance reduction pulses are superimposed on the plurality of stimulation pulses.

18. The controller of claim 16 or 17, wherein the skin resistance reduction pulses: each pulse carries a current of no more than 0.1 mA; and have a frequency between 1 Hz and 100,000 Hz.

19. The controller of claim 2, wherein the controller is configured to, when operating in the stimulation mode, cause the ES system to apply a plurality of sensory blocking pulses, wherein the sensory blocking pulses have an intensity lower than that of the stimulation pulses.

20. The controller of claim 19, wherein the sensory blocking pulse has a frequency between 0.1 Hz and 150 Hz.

21. An electrical stimulation (ES) system for receiving signal transmissions from and providing signal transmissions to a controller according to any one of claims 1 to 20.

22. The ES system of claim 21, further comprising clothing, wherein the clothing provides support for the relative arrangement of the electrodes in the electrode array and is configured to distribute the electrodes on at least one body part of the user.

23. A computer-readable medium comprising computer program code, the computer-readable medium being configured to cause a controller to operate as claimed in any one of claims 1 to 22.

24. A method for delivering electrical stimulation (ES) to a user's muscles using at least one ES system, the ES system comprising a controller and an electrode array including a plurality of electrodes for applying the electrical stimulation to the muscles, wherein the electrodes are further configured to measure electrical parameters between any one electrode of the electrode array and any other electrode of the electrode array, the method comprising the steps of: The controller provides a signal to the ES system to operate the electrode array in detection mode during a detection period. The signal causes the ES system to provide a plurality of electrical parameter detection burst pulse sequences during at least one detection period, wherein each electrical parameter detection burst pulse sequence includes one or more detection pulses, and each electrical parameter detection burst pulse sequence is configured not to provide muscle stimulation. as well as The controller detects one or more detection parameters indicating the degree of muscle activity associated with each electrical parameter detection burst pulse sequence, wherein each electrical parameter detection burst pulse sequence is provided by applying a potential difference between different pairs of the plurality of electrodes, wherein an electrode pair refers to a combination of a first detection electrode and a second detection electrode selected from any electrode of the electrode array, such that when the controller provides a subsequent electrical parameter detection burst pulse sequence, the corresponding electrode pair for the subsequent electrical parameter detection burst pulse sequence includes any pair of two electrodes of the electrode array, except for any electrode pair corresponding to a previously provided electrical parameter detection burst pulse sequence of the detection period; as well as The controller calculates the electrical parameters between each pair of detection electrodes based on the one or more detection parameters.

25. The method of claim 24, further comprising the following steps: The controller provides a signal to the ES system to operate the electrode array in a stimulation mode, the signal causing the ES system to provide a plurality of stimulation pulses spaced apart by rest periods, wherein: Each stimulation pulse includes applying a stimulation potential difference between a first stimulation electrode and a second stimulation electrode in the electrode array, such that the stimulation potential difference is configured to provide stimulation to the muscle; and Each rest period includes a time when there are no stimulating pulses.

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