Patent Application
20240016432
Devices, systems, and methods herein relate to electromyography (EMG) that may be used in diagnostic and/or therapeutic applications, including but not limited to electrophysiological study of muscles in the body relating to neuromuscular function and/or disorders.
EMG relates to the study of electrical activity occurring in peripheral nerve and muscle tissue. There are typically two types of techniques for recording EMG signals: intramuscular or needle EMG (NEMG) and surface EMG (SEMG). A needle EMG procedure includes inserting a needle electrode directly into the muscle to be examined. Needle EMG is considered the clinical gold standard for assessing an array of neurophysiologic characteristics of muscle tissue for neuromuscular disease and may provide data related to the muscles and nerves (e.g., motor neurons) that control them. For example, NEMG data may permit characterization of neuromuscular function including spontaneous activity, motor unit action potential (MUAP) recruitment, activation, and morphology. However, NEMG is an invasive procedure that necessarily penetrates tissue and which may cause pain, as well as increase the risk of infection and disease transmission. For example, needle insertion may cause swelling and bleeding, and in some instances, viscus perforation. Some areas of the body may be particularly sensitive to insertion of a needle electrode such as the mouth, pharynx, eyes, ears, gastrointestinal (GI) tract, urinary system, myocardium, and the like.
SEMG is a non-invasive and pain free EMG technique that may be used to assess muscle function by receiving electrical activity of one or more muscles from surface electrodes placed on the skin above the muscles to be examined. Surface EMG signals may be recorded over a prolonged period of time from many sites and motor units, and even when the patient is undergoing physical activity. Surface EMG is considered an acceptable technique for kinesiologic analysis of movement disorders. However, SEMG data may have limited spatial resolution relative to NEMG data due to the large surface area of SEMG sensors. For example, SEMG data may be susceptible to mechanical and electrical artifacts as well as cross-talk between adjacent muscles. Therefore, typical SEMG techniques do not reliably permit characterization of insertional activity, spontaneous activity, motor unit size and shape, and/or interference pattern. The American Academy of Neurology has concluded that SEMG is substantially inferior to NEMG for the evaluation of neuromuscular disorders. Therefore, additional devices, systems, and methods for performing electromyography may be desirable.
Described herein are sensor assemblies and methods for non-invasively generating an EMG signal corresponding to muscle tissue where the sensor may be positioned directly on a surface of the muscle tissue including any associated membrane (e.g., mucosal, endothelial, synovial), dermal tissue or connective tissue overlying the muscle tissue. These systems and methods may also be used to permit evaluation of neuromuscular function and/or diagnosis of neuromuscular conditions associated with muscle tissue located within a moist body cavity. Conventional non-invasive EMG devices and techniques such as SEMG record electrical activity of a large surface area corresponding to muscle tissue and may have limited accuracy and utility due to muscle cross-talk (e.g., electrical interference from adjacent muscles) and noise due to moisture between a sensor and tissue (e.g., muscle having a mucosal lining). On the other hand, conventional invasive EMG devices and techniques such as NEMG may cause pain and/or damage to muscle tissue, thereby limiting their use in sensitive tissue systems (e.g., internal organ systems) and adding procedural complexity (e.g., use of general anesthesia).
Generally, the systems and methods described herein may use a sensor to contact an intact tissue surface to receive electrical activity signal data of a specific muscle through any overlying membrane without penetrating or piercing a surface of the tissue. The sensor may include a pair of rounded electrodes configured to directly press against and elastically deform the tissue surface so as to form a temporary indentation while the sensor receives electrical activity data of muscle underlying the surface. The sensor may be configured to provide repeatable signal measurements of an isolated muscle rather than a broader surface area encompassing a group of muscles. Neuromuscular function may be characterized and evaluated using the acquired sensor data.
In some variations, a sensor assembly is provided, comprising a sensor including a first electrode, a second electrode, and a sensor housing coupling the first and second electrodes. The first and second electrodes may project from a surface of the sensor housing for a projection length and are spaced apart by a spacing distance. A first ratio of the spacing distance to the projection length may be between about 0.075:1 and about 1.5:1.
In some of these variations, the first ratio may be between about 0.15:1 and about 0.75:1. In some variations, a second ratio of a diameter of the first and second electrodes to the spacing distance may be between about 0.2:1 and about 5:1. In some of these variations, the second ratio may be between about 0.4:1 and about 2.5:1. In some variations, a third ratio of a diameter of the first and second electrodes to the projection length may be between about 0.075:1 and about 1.5:1. In some of these variations, the third ratio may be between about 0.15:1 and about 0.75:1.
In some variations, the first and second electrodes may each comprise a rounded distal end. The first and second electrodes may be in parallel. The sensor housing may be configured to electrically isolate the first electrode from the second electrode. The first electrode may be configured as a reference electrode and the second electrode may be configured as an active electrode. The spacing distance may be between about 0.2 mm and about 1.0 mm. The projection length may be between about 0.5 mm and about 3 mm.
In some other variations, a sensor assembly is provided, comprising a sensor including a first electrode, a second electrode electrically isolated from the first electrode, and a sensor housing coupling the first and second electrodes. The first and second electrodes may project in parallel from a surface of the sensor housing. A distance between central longitudinal axes of the first and second electrodes may be between about 0.30 mm and about 2.0 mm.
In some variations, the first and second electrodes may project from the surface of the housing for a projection length between about 0.5 mm and about 3 mm. A diameter of the first and second electrodes may be between about 0.1 mm and about 1.0 mm. The distance may be between about 0.60 mm and about 1.5 mm.
In some variations, the sensor assembly may comprise a probe comprising one or more of the sensors and a handle portion. The probe may comprise a first portion and a second portion detachably attached to the first portion. In some of these variations, the first portion may comprise a paddle shape and a radius of curvature of between about 10 cm and about 20 cm. Adjacent sensors may be spaced apart from each other between about 0.5 cm and about 5 cm. In some of these variations, the probe may comprise one or more dental markers. In some variations, the probe may further comprise a rigid catheter. In other variations, the probe may further comprise a flexible catheter.
In some variations, the assembly may further comprise an amplifier coupled to the probe. The amplifier may comprise a pre-amplifier and/or a main amplifier. A controller may be coupled to the probe and the amplifier. The controller may comprise a processor and a memory. The controller may be configured to receive signal data corresponding to electrical activity of muscle tissue using the one or more sensors. The signal data may be amplified and used to generate electromyography data.
Also described here are methods for using a sensor probe. In general, these methods include the steps of advancing and positioning the probe into a body cavity and sensing activity in the muscle tissue using the sensor. The probe may comprise one or more sensors each comprising a first electrode, a second electrode, and a sensor housing coupling the first and second electrodes. The first and second electrodes may project from a surface of the sensor housing for a projection length and may be spaced apart by a spacing distance. A first ratio of the spacing distance to the projection length may be between about 0.075:1 and about 1.5:1. One or more sensors of the probe may be applied directly on an intact tissue surface so as to elastically deform the tissue surface. Signal data corresponding to electrical activity of tissue may be received using one or more sensors without penetrating or piercing the intact tissue surface.
In some variations, the tissue surface may comprise a membrane overlying the tissue surface. The tissue surface may be maintained in an unbroken state while applying one or more sensors of the probe directly on the tissue surface. The signal data may be processed and used to generate electromyography data.
Described herein are sensor devices, systems, and methods for use in non-invasive diagnostic procedures of neuromuscular function of tissue in a body cavity or on a surface of an anatomical structure. In some variations, a sensor assembly may be used for measuring electrical activity of one or more muscles. Generally, a non-invasive transmembrane EMG (TM-EMG) sensor may be used to receive electrical activity signal data corresponding to a specific muscle, with the signal data used to generate EMG data. One or more of the sensors may be incorporated into one or more sensor arrays in a probe. The probe and sensor arrays may be configured to contact muscle tissue in a membranous body cavity (e.g., oropharynx, abdominal cavity, pelvic cavity, joint cavity) or other anatomical structure (e.g., eyes), including anatomical structures accessed intraoperatively.
A sensor assembly as described herein may include one or more pairs of closely spaced, atraumatic electrodes in a bipolar or multipolar configuration. For example, a first electrode may be configured as a reference electrode and a second electrode may be configured as an active electrode. The first and second electrodes may be applied against a surface of muscle tissue (that may include a membrane overlying the muscle) and receive electrical activity signal data corresponding to an electrical potential difference (e.g., voltage) of the portion of muscle between the electrodes. Each electrode may comprise a shape to project or extend into the target muscle tissue. For example, the electrodes may comprise a generally cylindrical shape having a semispherical distal end. The electrodes may be applied against the muscle such that muscle tissue contacts the distal end and/or distal portions of the electrode. However, the shape, length, and spacing of the electrodes are such that the contact is atraumatic and does not damage the muscle (e.g., tear, penetrate the surface). Common noise between the first and second electrodes may be reduced due to the close spacing between the first and second electrode, thereby increasing the SNR of the signal and increasing specificity of the signal data. The atraumatic configuration of the sensor further permits stable and reproducible measurements using the sensor assemblies. Furthermore, the sensor assemblies as described herein may be used in areas of the body that are not typically assessed with NEMG and SEMG. For example, the sensor assemblies as described herein may be used within body cavities and their associated internal organ systems during a surgery or invasive procedure. For example, the sensor assemblies may contact moist muscle tissue having an overlying membrane (e.g., mucosal, endothelial, synovial).
In variations where a controller including a processor and memory are coupled to a TM-EMG sensor, the processor may generate EMG data using the signal data received from the TM-EMG sensor. EMG data generated from the sensor data may correspond to native or spontaneous neuromotor activity and/or a superposition of the evoked action potentials of the active motor units in the measured muscle. The EMG data may have a signal-to-noise ratio (SNR) that permits evaluation of neuromuscular function according to parameters such as insertional activity. spontaneous activity, motor unit size and shape, and interference pattern using sensor data acquired from the devices and systems as described herein.
In some variations, a probe having one or more sensors may be disposed in a housing (e.g., probe) having a size and shape matching a contour of the tissue to be evaluated. Intermediate and proximal portions of the probe may comprise a configuration to aid advancement of the probe to a target muscle. For example, portions of the probe may be flexible or rigid. In some of these variations, a probe may be advanced into a body cavity of interest using a delivery device such as a catheter or endoscope.
Described herein are electrode sensors for use in measuring electrical activity of one or more muscles. The electrodes may be unipolar, bipolar, or multipolar, and each electrode may comprise a different configuration.
The first electrode (120) and the second electrode (122) may comprise an atraumatic configuration to reduce or prevent damage to tissue damage during contact and/or signal acquisition with the sensor (100). For example, each of the electrodes (120, 122) may comprise a cylindrical body and a semi-spherical or other rounded distal end. In other variations, the electrodes may comprise other shapes (e.g., rectangular body, blunted distal end, rounded edges, flat surfaces, protruding surfaces, smooth surfaces, rough surfaces, grooved surfaces, indented surfaces, mixed surfaces) that are atraumatic to tissue. As another example, one or more of the electrodes may comprise a curved shape (e.g., C-shaped) and/or one or more bends.
In some variations, the first electrode (120) and the second electrode (122) may be parallel to each other. In other variations, the first and second electrodes (120, 122) may be angled non-parallel to each other. For example, the first and second electrodes (120, 122) may form a V-shaped projection relative to each other projecting from the housing (110).
In some variations, as shown in
The electrodes (120, 122) of the sensor (100) may comprise dimensions such that the electrode pair is atraumatic when in contact with muscle tissue. The dimensions described herein permit the electrodes to measure electrical activity of muscle tissue. In some variations, the electrodes (120, 122) may comprise a diameter (126, 128) between about 0.1 mm and about 1.0 mm. In some variations, the electrodes (120, 122) may comprise a diameter (126, 128) between about 0.3 mm and about 0.75 mm. In some variations, the electrodes (120, 122) may comprise a projection length (124) between about 0.5 mm and about 3.0 mm. In some variations, the electrodes (120, 122) may comprise a projection length (124) between about 0.5 mm and about 2.5 mm. In some variations, the electrodes (120, 122) may comprise a projection length (124) between about 1.0 mm and about 2.0 mm. In some variations, the electrodes (120, 122) may comprise a total length (e.g., projection length and insulated length) of between about 0.5 mm and about 5.0 mm.
The dimensions described herein permit the electrodes to measure electrical activity of muscle tissue atraumatically and with specificity to evaluate neuromuscular function of desired tissue. The electrodes (120, 122) of the sensor (100) may comprise a spacing distance (118) configured such that desired muscle tissue may be isolated while permitting a potential difference of muscle between the electrodes to be measured. For example, the electrode spacing (118) of the bipolar sensor (100) disclosed herein is such that common noise between the electrodes (120, 122) may be reduced to thereby improve an SNR of the bipolar sensor signal data. For example, a smaller spacing distance (118) corresponds to a more focused and precise measurement of muscle while a larger spacing distance (118) corresponds to a more general measurement of the muscle. In some variations, the electrodes (120, 122) may comprise a spacing distance (118) between about 0.2 mm and about 1.0 mm. In some variations, the electrodes (120, 122) may comprise a spacing distance (118) between about 0.3 mm and about 0.75 mm. In other variations, the electrodes (120, 122) may comprise a spacing distance between a first central longitudinal axis (e.g., through the center or midpoint) of the first electrode and a second central longitudinal axis of the second electrode may be between about 0.3 mm and about 2.0 mm. In some other variations, the electrodes (120, 122) may comprise a spacing distance between a first central longitudinal axis of the first electrode and a second central longitudinal axis of the second electrode of between about 0.6 mm and about 1.5 mm.
The sensors described herein may permit the electrodes to measure electrical activity of muscle tissue atraumatically and with specificity to evaluate neuromuscular function based on one or more relationship(s) between the dimensions of the electrodes. For example, electrode dimensions including spacing distance, electrode length, and electrode diameter may be related such that the electrodes are spaced close enough to permit voltage measurement of desired muscle tissue and the shape and dimensions of the electrodes are atraumatic to reduce damage to tissue (e.g., tissue piercing). In some variations, a first ratio of the spacing distance (118) to the projection length (124) may be between about 0.075 and about 1.5:1. In some variations, a first ratio of the spacing distance (118) to the projection length (124) may be between about 0.15:1 and about 0.75:1. In some variations, a second ratio of a diameter of the first and second electrodes (120, 122) to the spacing distance (118) may be between about 0.2:1 and about 5:1. In some variations, the second ratio of a diameter of the first and second electrodes (120, 122) to the spacing distance (118) may be between about 0.4:1 and about 2.5:1. In some variations, a third ratio of a diameter of the first and second electrodes (120, 122) to the projection length (124) may be between about 0.075:1 and about 1.5:1. In some variations, the third ratio of a diameter of the first and second electrodes (120, 122) to the projection length (124) may be between about 0.15:1 and about 0.75:1.
The electrodes as described herein may be formed of any biocompatible conductive metal and/or alloy including, but not limited to tungsten, silver, platinum, platinum-iridium, nickel titanium alloys, copper-zinc-aluminum-nickel alloys, copper-aluminum-nickel alloys, combinations thereof, and the like. The lead wires described herein may comprise an electrically conductive wire configured to connect the electrodes of a bipolar sensor to other components of a sensor assembly, such as an amplifier, controller, and the like. The amplifier may comprise a pre-amplifier, either alone or in combination with another amplifier. In some variations, each electrode may be coupled to a respective insulated lead wire. The lead wires (130, 132) of a pair of electrodes (120, 122) may be configured as a twisted pair (e.g., braided). This twisting may reduce the electromagnetic interference and/or crosstalk from other pairs of lead wires in the device. The number of twists per inch may be in the range of about 0.5 to about 5 twists per inch, and different pairs may have different twists per inch. The lead wires as described herein may comprise any length necessary to couple its corresponding electrode to the sensor assembly. In some variations, the lead wire may comprise a length of between about 0.1 m and about 2.0 m. In some variations, the lead wire may comprise a length of between about 0.5 m and about 1.5 m. In some variations, the lead wire may have about the same diameter as its corresponding electrode. The lead wires as described herein may be formed of any electrically conductive metal and/or biocompatible conductive metal and/or alloy including, but not limited to copper, silver, platinum, platinum-iridium, combinations thereof, and the like. In some variations, the lead wires may comprise a touch proof, single pole connector (e.g., DIN 42-802) at a proximal end. In some variations, the lead wires may be stranded or solid.
One or more portions of the lead wires may be flexible or semi-flexible, one or more portions may be rigid or semi-rigid, and/or one or more portions of the lead wires may transition between flexible and rigid configurations. The lead wires described herein may be made of any material or combination of materials. For example, the lead wires may be insulated using one or more polymers (e.g., silicone, polyvinyl chloride, latex, polyurethane, polyethylene, PTFE, nylon).
In some variations, the sensors described herein may comprise a ground electrode and a corresponding ground wire configured to reduce noise. The ground electrode and ground wire may be separate from or integrated with the sensor in a housing. The ground electrode and ground wire may be formed of any biocompatible conductive metal and/or alloy including, but not limited to tungsten, silver, platinum, platinum-iridium, nickel titanium alloys, copper-zinc-aluminum-nickel alloys, copper-aluminum-nickel alloys, combinations thereof, and the like.
In some variations, the sensor may be configured as a multipolar sensor with three or more of the electrodes as described herein. The electrodes of a multipolar sensor may be configured to optimize surface area contact with predetermined muscle tissue, thereby increasing the SNR of the signal and specificity of the signal data.
In some variations, the sensor electrodes, ground electrode and lead wires as described herein may be integrated into a single cable. For example, the cable may comprise one or more layers of shielding and insulation. In some variations, the shielding and insulation layers may be disposed individually over one or more of the sensor and ground electrodes and/or disposed over the cable as a whole. The ground electrode of a single cable may comprise an interwoven mesh or spiral shape with helical, wrapped strands. In some variations, the cable may comprise one or more ground electrodes. For example, the cable may comprise a ground electrode for each sensor electrode. The lead wires of the cable may be stranded or solid. For example, the number of strands may be between about 7 and about 100.
As shown in
A sensor assembly may include one or more of the components necessary to measure and evaluate muscle tissue using the bipolar or multipolar sensors as described herein. The sensor assembly may couple to one or more computer systems and/or networks.
A sensor assembly (500), as depicted in
The controller (520) may be implemented consistent with numerous general purpose or special purpose computing systems or configurations. Various exemplary computing systems, environments, and/or configurations that may be suitable for use with the systems and devices disclosed herein may include, but are not limited to software or other components within or embodied on personal computing devices, network appliances, servers or server computing devices such as routing/connectivity components, portable (e.g., hand-held) or laptop devices, multiprocessor systems, microprocessor-based systems, and distributed computing networks. Examples of portable computing devices include smartphones, personal digital assistants (PDAs), cell phones, tablet PCs, phablets (personal computing devices that are larger than a smartphone, but smaller than a tablet), wearable computers taking the form of smartwatches, portable music devices, and the like, and portable or wearable augmented reality devices that interface with an operator's environment through sensors and may use head-mounted displays for visualization, eye gaze tracking, and user input.
The processor (522) may be any suitable processing device configured to run and/or execute a set of instructions or code and may include one or more data processors, image processors, graphics processing units, physics processing units, digital signal processors, and/or central processing units. The processor (522) may be, for example, a general purpose processor, Field Programmable Gate Array (FPGA), an Application Specific Integrated Circuit (ASIC), and/or the like. The processor (522) may be configured to run and/or execute application processes and/or other modules, processes and/or functions associated with the system and/or a network associated therewith. The underlying device technologies may be provided in a variety of component types, e.g., metal-oxide semiconductor field-effect transistor (MOSFET) technologies like complementary metal-oxide semiconductor (CMOS), bipolar technologies like emitter-coupled logic (ECL), polymer technologies (e.g., silicon-conjugated polymer and metal-conjugated polymer-metal structures), mixed analog and digital, and/or the like.
In some variations, the memory (524) may include a database (not shown) and may be, for example, a random access memory (RAM), a memory buffer, a hard drive, an erasable programmable read-only memory (EPROM), an electrically erasable read-only memory (EEPROM), a read-only memory (ROM), Flash memory, and the like. As used herein, database refers to a data storage resource. The memory (524) may store instructions to cause the processor (522) to execute modules, processes and/or functions associated with the sensor assembly (500), such as probe control, signal data processing, EMG data processing, sensor control, communication, and/or user settings. In some variations, storage may be network-based and accessible for one or more authorized users. Network-based storage may be referred to as remote data storage or cloud data storage. EMG signal data stored in cloud data storage (e.g., database) may be accessible to respective users via a network, such as the Internet. In some variations, database (120) may be a cloud-based FPGA.
Some variations described herein relate to a computer storage product with a non-transitory computer-readable medium (also may be referred to as a non-transitory processor-readable medium) having instructions or computer code thereon for performing various computer-implemented operations. The computer-readable medium (or processor-readable medium) is non-transitory in the sense that it does not include transitory propagating signals per se (e.g., a propagating electromagnetic wave carrying information on a transmission medium such as space or a cable). The media and computer code (also may be referred to as code or algorithm) may be those designed and constructed for the specific purpose or purposes. Examples of non-transitory computer-readable media include, but are not limited to, magnetic storage media such as: hard disks: floppy disks: magnetic tape: optical storage media such as Compact Disc/Digital Video Discs (CD/DVDs): Compact Disc-Read Only Memories (CD-ROMs): holographic devices: magneto-optical storage media such as optical disks: solid state storage devices such as a solid state drive (SSD) and a solid state hybrid drive (SSHD): carrier wave signal processing modules: and hardware devices that are specially configured to store and execute program code, such as Application-Specific Integrated Circuits (ASICs), Programmable Logic Devices (PLDs), Read-Only Memory (ROM), and Random-Access Memory (RAM) devices. Other variations described herein relate to a computer program product, which may include, for example, the instructions and/or computer code disclosed herein.
The systems, devices, and/or methods described herein may be performed by software (executed on hardware), hardware, or a combination thereof. Hardware modules may include, for example, a general-purpose processor (or microprocessor or microcontroller), a field programmable gate array (FPGA), and/or an application specific integrated circuit (ASIC). Software modules (executed on hardware) may be expressed in a variety of software languages (e.g., computer code), including C, C++, Java®, Python, Ruby, Visual Basic®, and/or other object-oriented, procedural, or other programming language and development tools. Examples of computer code include, but are not limited to, micro-code or micro-instructions, machine instructions, such as produced by a compiler, code used to produce a web service, and files containing higher-level instructions that are executed by a computer using an interpreter. Additional examples of computer code include, but are not limited to, control signals, encrypted code, and compressed code.
A sensor assembly (500), as depicted in
The communication interface (544) may permit an operator to interact with and/or control the sensor assembly (500) directly and/or remotely. For example, a user interface (544) of the sensor assembly (500) may include an input device for an operator to input commands and an output device for an operator and/or other observers to receive output (e.g., view patient data on a display device) related to operation of the sensor assembly (500). In some variations, a network interface (542) may permit the sensor assembly (500) to communicate with one or more of a network (560) (e.g., Internet), remote server (564), and database (562) as described in more detail herein.
User interface (544) may serve as a communication interface between an operator and the sensor assembly (500). In some variations, the user interface (544) may comprise an input device and output device (e.g., touch screen and display) and be configured to receive input data and output data from one or more of the probe (510), delivery device (550), input device, output device, network (560), database (562), and server (564). For example, images generated by an optical sensor of a delivery device (550) (e.g., an endoscope) may be processed by processor (522) and memory (524), and displayed by the output device (e.g., monitor display). Sensor data from one or more sensors (512, 514) may be received by user interface (544) and output visually and/or audibly through one or more output devices. As another example, operator control of an input device (e.g., joystick, keyboard, touch screen) may be received by user interface (544) and then processed by processor (522) and memory (524) for user interface (544) to output a control signal to one or more probes (510) and delivery devices (550).
An output device of a user interface (544) may output sensor data corresponding to a patient and/or sensor assembly (500), and may comprise one or more of a display device and audio device. The output device may be coupled to a patient platform and/or disposed on a medical cart adjacent to the patient and/or operator. In other variations, the output device may be mounted to any suitable object, such as furniture (e.g., a bed rail), a wall, a ceiling, and may be self-standing.
The display device may be configured to display a graphical user interface (GUI). A display device may permit an operator to view signal data, EMG data, and/or other data processed by the controller (520) such as images of one or more body cavities and tissue. For example, an endoscope comprising an optical sensor (e.g., camera) located in a body cavity or lumen of a patient may be configured to image an internal view of the body cavity and/or muscle tissue to be measured. In some variations, an output device may comprise a display device including at least one of a light emitting diode (LED), liquid crystal display (LCD), electroluminescent display (ELD), plasma display panel (PDP), thin film transistor (TFT), organic light emitting diodes (OLED), electronic paper/e-ink display, laser display, and/or holographic display.
An audio device may audibly output patient data, sensor data, system data, alarms, and/or warnings. For example, the audio device may output an audible warning when monitored patient data (e.g., temperature, heart rate) falls outside a predetermined range or when a malfunction in the probe (510) is detected. In some variations, an audio device may comprise at least one of a speaker, piezoelectric audio device, magnetostrictive speaker, and/or digital speaker. In some variations, an operator may communicate with other users using the audio device and a communication channel. For example, the operator may form an audio communication channel (e.g., VOIP call) with a remote operator and/or observer.
Some variations of an input device may comprise at least one switch configured to generate a control signal. The input device may be coupled to a patient platform and/or disposed on a medical cart adjacent to the patient and/or operator. However, the input device may be mounted to any suitable object, such as furniture (e.g., a bed rail), a wall, a ceiling, or may be self-standing. In some variations, the input device may comprise a wired and/or wireless transmitter configured to transmit a control signal to a wired and/or wireless receiver of a controller (520). For example, an input device may comprise a touch surface for an operator to provide input (e.g., finger contact to the touch surface) corresponding to a control signal. An input device comprising a touch surface may be configured to detect contact and movement on the touch surface using any of a plurality of touch sensitivity technologies including capacitive, resistive, infrared, optical imaging, dispersive signal, acoustic pulse recognition, and surface acoustic wave technologies. In variations of an input device comprising at least one switch, a switch may comprise, for example, at least one of a button (e.g., hard key, soft key), touch surface, keyboard, analog stick (e.g., joystick), directional pad, pointing device (e.g., mouse), trackball, jog dial, step switch, rocker switch, pointer device (e.g., stylus), motion sensor, image sensor, and microphone. A motion sensor may receive operator movement data from an optical sensor and classify an operator gesture as a control signal. A microphone may receive audio and recognize an operator voice as a control signal.
As depicted in
In some variations, the network interface (542) may comprise a radiofrequency receiver, transmitter, and/or optical (e.g., infrared) receiver and transmitter configured to communicate with one or more devices and/or networks. The network interface (542) may communicate by wires and/or wirelessly with one or more of the probe (510), delivery device (550), user interface (544), network (560), database (562), and server (564).
In some variations, the network interface (542) may comprise radiofrequency (RF) circuitry (e.g., RF transceiver) including one or more of a receiver, transmitter, and/or optical (e.g., infrared) receiver and transmitter configured to communicate with one or more devices and/or networks. RF circuitry may receive and transmit RF signals (e.g., electromagnetic signals). The RF circuitry converts electrical signals to/from electromagnetic signals and communicates with communications networks and other communications devices via the electromagnetic signals. The RF circuitry may include one or more of an antenna system, an RF transceiver, one or more amplifiers, a tuner, one or more oscillators, a digital signal processor, a CODEC chipset, a subscriber identity module (SIM) card, memory, and the like. A wireless network may refer to any type of digital network that is not connected by cables of any kind. Examples of wireless communication in a wireless network include, but are not limited to cellular, radio, satellite, and microwave communication. The wireless communication may use any of a plurality of communications standards, protocols and technologies, including but not limited to Global System for Mobile Communications (GSM), Enhanced Data GSM Environment (EDGE), high-speed downlink packet access (HSDPA), wideband code division multiple access (W-CDMA), code division multiple access (CDMA), time division multiple access (TDMA), Bluetooth, near-field communication (NFC), radio-frequency identification (RFID), Wireless Fidelity (Wi-Fi) (e.g., IEEE 802.11a, IEEE 802.11b, IEEE 802.11g and/or IEEE 802.11n), voice over Internet Protocol (VOIP), Wi-MAX, a protocol for email (e.g., Internet Message Access Protocol (IMAP) and/or Post Office Protocol (POP)), instant messaging (e.g., extensible Messaging and Presence Protocol (XMPP), Session Initiation Protocol for Instant Messaging and Presence Leveraging Extensions (SIMPLE), and/or Instant Messaging and Presence Service (IMPS)), and/or Short Message Service (SMS), or any other suitable communication protocol. Some wireless network deployments combine networks from multiple cellular networks or use a mix of cellular, Wi-Fi, and satellite communication. In some variations, a wireless network may connect to a wired network in order to interface with the Internet, other carrier voice and data networks, business networks, and personal networks. A wired network is typically carried over copper twisted pair, coaxial cable, and/or fiber optic cables. There are many different types of wired networks including, but not limited to, wide area networks (WAN), metropolitan area networks (MAN), local area networks (LAN), Internet area networks (IAN), campus area networks (CAN), global area networks (GAN), like the Internet, and virtual private networks (VPN). As used herein, network refers to any combination of wireless, wired, public, and private data networks that are typically interconnected through the Internet, to provide a unified networking and information access system.
In some variations, the sensor assembly (500) may comprise an analog-to-digital converter (not shown) configured to convert an analog voltage signal into a digital voltage signal. The accuracy of the signal conversion may depend on the sampling frequency and the number of steps (e.g., vertical resolution). For example, a high sampling frequency and a large number of steps may produce a more accurate digital replica of the received analog signal.
A probe (510) may comprise one or more of the bipolar or multipolar electrode sensors (512) configured to measure electrical activity of a set of muscles. The probe (510) may comprise a housing configured with a size, shape, and sensor arrangement suited for advancement into a body cavity or surface of an anatomical structure and the muscle(s) to be evaluated. For example, a transoral probe comprising a curved, rigid probe housing including at least two sensor arrays may be configured to contact and measure electrical activity of a group of muscles in an upper airway cavity. In another example, a rigid probe may comprise a single bipolar electrode sensor coupled to a rigid shaft. The probe configurations as described herein are merely illustrative.
In some variations, the devices, systems, and methods may comprise one or more elements described in International Application Serial No. PCT/US2015/018196, filed on Feb. 27, 2015, and titled “SYSTEMS, METHODS AND DEVICES FOR SENSING EMG ACTIVITY,” and/or U.S. Provisional Application Ser. No. 61/946,259, filed on Feb. 28, 2014, and titled “SYSTEMS, METHODS AND DEVICES FOR SLEEP APNEA,” each of which is hereby incorporated by reference in its entirety.
In some variations, the distal portion (202) and proximal portion (206) may comprise a combined length of between about 5 cm and about 30 cm. In some variations, the distal portion (202) and proximal portion (206) may comprise a combined length of between about 10 cm and about 20 cm. In some variations, the distal portion (202) and proximal portion (206) may comprise a combined length of about 16.5 cm. In some variations, the proximal portion (206) may comprise a length of between about 2 cm and about 20 cm. In some variations, the proximal portion (206) may comprise a length of between about 5 cm and about 10 cm. In some variations, the proximal portion (206) may comprise a length of about 8 cm. In some variations, the distal portion (202) may comprise a width of between about 1.5 cm and about 7 cm. In some variations, the distal portion (202) may comprise a width of between about 3 cm and about 4 cm. In some variations, the distal portion (202) may comprise a width of about 3.5 cm. In some variations, the proximal portion (206) may comprise a circumference of between about 1 cm and about 5 cm. In some variations, the proximal portion (206) may comprise a circumference of between about 2 cm and about 4 cm. In some variations, the proximal portion (206) may comprise a circumference of about 3 cm. In some variations, the distal portion (202) may comprise a paddle shape comprising a length of between about 4 cm and about 10 cm. In some variations, the paddle shape may comprise a length of between about 6 cm and about 8 cm. In some variations, the paddle shape may comprise a length of about 7.3 cm. In some variations, the distal portion (202) may comprise a width (215) of between about 0.5 cm and about 3.5 cm. In some variations, the distal portion (202) may comprise a width (215) of about 1.8 cm. In some variations, the distal portion (202) may comprise a radius of curvature of between about 10 cm and about 20 cm. In some variations, the distal portion (202) may comprise a radius of curvature of about 15 cm. The superior surface (244) of the probe (200) may comprise a convex curvature, and the inferior surface (246) may comprise a concave curvature.
The transoral probe (200) may be configured for placement adjacent to at least one of the soft palate, pharyngeal wall, and tongue of a patient, as described in more detail herein. For example, the size, shape, and other physical characteristics of a probe housing may be configured for an upper airway cavity of a patient to permit evaluation of muscle tissue. In some variations, as shown in
In some variations, the probe (200) may comprise one or more dental markers (217). For example, the dental markers (217) may comprise one or more indentations (e.g., notches) and/or protrusions (e.g., grooves) configured for one or more upper or lower teeth to bite into. In some variations, the dental markers (217) may be spaced apart between about 0.5 cm and about 1.5 cm. In some variations, the dental markers (217) may be spaced apart by about 1.0 cm. In some variations, the dental markers (217) may be disposed at least 5 mm away from a proximal end of the distal portion (202).
In some variations, a flexible printed circuit may be disposed in the distal portion (202) of the probe (200) and coupled to each of the bipolar or multipolar sensors (210). One or more flexible printed circuits may be configured to electrically connect the bipolar or multipolar sensors (210) to the cable (216). The flexible printed circuits are not particularly limited and may be a single-sided flex circuit, double-sided flex circuit, double access flex circuit, and the like.
The bipolar sensors (210) may comprise a first electrode (230) having a first diameter (236) and a second electrode (232) having a second diameter (238). In some variations, the electrodes (230, 232) may have a spacing distance (228) between each other and a projection length (234) from a surface of the housing portion (219). The shape, dimensions, and materials of the sensor (210) may be the same as those described herein with respect to bipolar sensor (100). The housing portion (219) may be formed on a surface of the first portion (204) (e.g., assembly housing).
The intermediate portion (304) may have any suitable dimensions. For example, the intermediate portion (304) may have any suitable length that allows the assembly (300) to be advanced from a point external to the body to a target location. In some variations, the length of the intermediate portion (304) may be between about 1 cm and about 100 cm. The intermediate portion (304) may have any suitable diameter, such as, for example, about 5.7 French, about 6.1 French, about 7 French, about 8.3 French, between about 5 French and about 9) French, between about 5 French and about 7 French, between about 6 French and about 9) French, and the like. The intermediate portion (304) may be removably attached from the proximal portion (306). In some variations, the distal portion (302) may be removably attached to the intermediate portion (304). In other variations, the distal portion (302) may be fixed to the intermediate portion (304).
The distal portion (302) may comprise one or more bipolar or multipolar sensors (308) each comprising a first electrode (320) having a first diameter (326) and a second electrode (322) having a second diameter (328). In some variations, the electrodes (320, 322) may have a spacing distance (318) between each other and a projection length (324) from a surface of the sensor housing portion (310). The housing portion (310) may have a housing length (316). The shape, dimensions, and materials of the bipolar sensor (308) may be the same as those described herein with respect to any of the bipolar sensors disclosed such as bipolar sensors (100, 200, 430, 512). The first and second electrodes (320, 322) may be coupled to respective lead wires (330, 332) through corresponding connectors (312, 314) (e.g., weld points) as described herein.
In some variations, a flexible printed circuit may be disposed in one or more of the intermediate portion (304) and the distal portion (306) of the assembly (300) and coupled to the bipolar or multipolar sensor (308). One or more flexible printed circuits may be configured to electrically connect the bipolar sensor (308) to a controller. Also, in some examples, the probe may be a flexible or malleable probe, or comprise a combination of one or more rigid sections, flexible sections and malleable sections.
In some variations, the delivery device may comprise an optical sensor (e.g., a charged coupled device (CCD) or complementary metal-oxide semiconductor (CMOS) optical sensor) and may be configured to generate an image signal that is transmitted to a display. For example, in some variations, the delivery device may comprise a camera with an image sensor (e.g., a CMOS or CCD array with or without a color filter array and associated processing circuitry). An external light source (e.g., laser, LED, lamp, or the like) may generate light that may be carried by fiber optic cables or one or more LEDs may be configured to provide illumination. For example, a fiberscope comprising a bundle of flexible optical fibers may be configured to receive and propagate light from an external light source. The fiberscope may comprise an image sensor configured to receive reflected light reflected from a body cavity. The image sensor may detect the reflected light and convert it into image signals that may be processed and transmitted for display. The endoscope may have any suitable configuration, for example, it may be a chip-on-the-tip camera endoscope, a three camera endoscope, and the like. The sensor probes may be configured for a forward, side or retro-facing direction.
In some variations, the delivery device (410) may be a catheter for angiography including, transvascular analysis of muscle activity such a myocardium, chordae, cardiac valves including tricuspid, mitral, pulmonic, and aortic valves. In some variations, the sensor assembly may be incorporated into robotic surgical systems, computer navigated surgery systems, and/or minimally invasive surgery systems. This may include using a tool or end effector provided on a robotic arm, catheter, endoscope or minimally invasive diagnostic or surgical device to be positioned on membranes in targeted areas of the gastrointestinal (GI) tract, urinary tract, and oropharyngeal cavity, for example.
The endoscope (410) may comprise a body portion (412) including a port (414) coupled to a catheter (416) having a distal end (417). The sensor assembly (430) may comprise a proximal portion (436) (e.g., handle), a flexible intermediate portion (434), and a distal portion (432). The sensor assembly (430) may be advanced through the port (414) and through the catheter (416) such that the distal portion (432) of the sensor assembly (430) is slidably advanced out of the distal end (417) of the catheter (416). The intermediate portion (434) may be sized to slidably advance within a lumen of the catheter (416). The proximal portion (436) may comprise a handle, insulated lead wires, and the like. In some variations, the proximal portion (436) may comprise a length in the range of between about 1 cm and about 3 m. The proximal portion (436) may be separated from the port (414) by a predetermined distance (446). In some variations, the distance from the port (414) to a handle may be in the range of between about 10 cm and about 30 cm.
The catheter (416) and intermediate portion (434) described herein may comprise any elongate body suitable for advancement through at least a portion of body lumen. The catheter (416) and intermediate portion (434) may be hollow, partially hollow, and/or partially solid. One or more portions of the catheter (416) and intermediate portion (434) may be flexible or semi-flexible, one or more portions may be rigid or semi-rigid, and/or one or more portions of the catheter (416) and intermediate portion (434) may be changed between flexible and rigid configurations. Flexible portions of the catheter (416) and intermediate portion (434) may allow the catheter (416) and intermediate portion (434) to be navigated (e.g., steerable) through tortuous body lumens to reach a desired target site. The catheter (416) and intermediate portion (434) described here may be made of any material or combination of materials. For example, the catheter (416) and intermediate portion (434) may comprise one or more metals or metal alloys (e.g., e.g., nickel titanium alloys, copper-zinc-aluminum-nickel alloys, copper-aluminum-nickel alloys, combinations thereof, and the like) and/or one or more polymers (e.g., silicone, polyvinyl chloride, latex, polyurethane, polyethylene, PTFE, nylon, combinations thereof, and the like) as described herein.
Catheter (416) and intermediate portion (434) may have any suitable dimensions. For example, catheter (416) and intermediate portion (434) may have any suitable length that allows those components to be advanced from a point external to the body to a target location. In some variations, the catheter (416) may have a length in the range of between about 20 cm and about 200 cm. Catheter (416) and intermediate portion (434) may have any suitable diameter, such as, for example, about 5.7 French, about 6.1 French, about 7 French, about 8.3 French, between about 5 French and about 9 French, between about 5 French and about 7 French, between about 6 French and about 9 French, and the like. The intermediate portion (434) may be removably attached to the proximal portion (436). In some variations, the bipolar sensor (438) may be removably attached to the intermediate portion (434).
The bipolar or multipolar sensor (438) may be disposed within a distal portion (432) of the sensor assembly (430). The bipolar sensor (438) may comprise a sensor housing (440) coupled to a first electrode (442) and a second electrode (444). The shape, dimensions, and materials of the bipolar sensor (438) may be the same as those described herein with respect to any of the bipolar sensors disclosed such as bipolar sensors (100, 200, 312, 512).
Also described here are methods for non-invasively generating an EMG signal corresponding to muscle tissue using the systems and devices described herein. The methods described here may permit EMG data to be gathered from difficult to reach tissue and measure locations such as moist body cavities and organ systems. This may have numerous benefits, such as permitting evaluation and diagnosis of a range of neuromuscular conditions. Conventional EMG techniques may be inadequate for generating EMG data in many body cavities and organ systems. For example, NEMG in body cavities and organ systems has limited clinical use due to a higher risk of damage to tissue. SEMG may be inadequate for evaluating neuromuscular function due to its lower spatial resolution and contamination from one or more electrical, mechanical, and movement artifacts. Furthermore, SEMG systems having adhesive surface electrodes may not be appropriate for organ systems and moist body cavities.
Generally, the methods described here include advancing a sensor probe into a body cavity to contact a tissue surface, and receive signal data without penetrating or piercing the intact tissue surface. The signal data may be processed and used to generate electromyography data. It should be appreciated that any of the systems and devices described herein may be used in the methods described herein.
The probe may be applied directly on intact tissue to elastically deform the tissue surface (604). For example, the probe may atraumatically contact the surface of target tissue and/or a membrane overlying the target tissue. Neither the sensors nor probe penetrates or pierces the intact target tissue. In some variations, the probe may contact the target tissue and/or membrane at an angle between about 60 degrees and about 120 degrees with respect to a surface of the target tissue and/or membrane in contact with the probe. For example, the probe may be perpendicular to the target tissue and/or membrane. In some variations, the probe may contact the target tissue at a midpoint of the muscle to avoid tendinous insertions.
Signal data may be received by the sensors of the probe without penetrating the intact tissue surface (606). For example, the probe may remain in continuous contact with the intact tissue as electrical activity of the target tissue is received by the probe. The tissue surface may be maintained in an unbroken state while applying the one or more sensors of the probe directly on the tissue surface. A determination whether to reposition the sensor probe (608) may be performed. If so, the probe may be moved and steps 604 and 606 repeated. The signal data received by the sensor probe may be processed (610). For example, the electrical activity signal data received by the probe may be amplified by an amplifier of a controller and/or undergo additional filtering in real-time as the data is being received.
Electromyography data may be generated using the processed signal data (612). For example, the processed signal data may be compared against a threshold (e.g., benchmark activity level) to generate EMG data. In some variations, the EMG data may be generated and displayed to a user in real-time to permit the user to determine if the sensor probe should be repositioned. The received and/or processed signal data and generated EMG data may be stored in memory locally, on another device, and/or over a network (e.g., cloud storage, remote server). The sensor probe may be removed from the target tissue and retracted away from the patient.
The systems, devices, and methods described here may be used throughout the body to generate EMG data and permit evaluation of neuromuscular function and/or diagnosis of neuromuscular conditions, examples of which are described in more detail herein.
Conventionally, usage of NEMG in a pharynx and/or tongue is difficult to perform because an awake patient may suffer from one or more of insertion pain, gag reflex, procedure fear, local trauma, and bleeding. Any of these factors may limit needle electrode placement in the transoral cavity. General anesthesia may be used to reduce some of these issues, but the use of anesthesia adds complexity, cost, and other possible complications to the procedure. In some variations, a sensor assembly may comprise a transoral (e.g., airway) probe configured to contact the mucosa and measure electrical activity of one or more of the underlying muscle tissues such as a palatopharyngeus, palatoglossus, musculus uvulae, vocal cord muscles, intrinsic tongue muscle, genioglossus, cricopharyngeus, tensor veli palatini, levator veli palatini, interarytenoideus, cricoarytenoids, cricothyroid, constrictor muscles, upper esophageal sphincter, lower esophageal sphincter, gastroduodenal sphincter, sphincter of Oddi, gastric, and paraspinal, as described in detail herein.
In variations where a rigid sensor probe is used transorally, the rigid sensor probe may be inserted through a patient's mouth and advanced toward one or more muscles to be measured such as in the nasopharynx, oropharynx, hypopharynx, larynx, esophagus, and GI tract. In other variations, a rigid sensor probe may be used with a visualization device such as a rigid straight laryngoscope, rigid laryngeal strobe scope, rigid curved laryngoscope, rigid bronchoscope, rigid esophagoscope, and rigid diverticuloscope to measure.
In variations where a flexible sensor probe is used transorally, the flexible sensor probe may be inserted through a patient's mouth and advanced toward one or more muscles to be measured. In some other variations, a flexible sensor probe may be used with a visualization device such as a flexible fiber optic rhinolaryngoscope, flexible fiber optic bronchoscope, flexible fiber optic esophagoscope. For example, the flexible sensor probe may be slidably advanced through a lumen of the flexible visualization device.
To illustrate some of the methods of using a sensor probe, some of the muscles that may be sensed by the probes described herein are illustrated with respect to the
For example, the probe may be configured to contact the mucosa overlying a side of the musculus uvulae (702) projecting (e.g., descending) from a posterior edge of the middle of the soft palate (704). The probe may be configured to contact the mucosa overlying one or more of the posterior fasciculus and anterior fasciculus of the palatopharyngeus (706). The probe may be configured to contact the mucosa overlying one or more of the four intrinsic muscles that extend along a length of the tongue including the superior longitudinal muscle that extends along an upper surface of the tongue, the inferior longitudinal muscle that extends along a side of the tongue (701), the vertical muscle located along the middle of the tongue (701) (and which joins the superior and inferior and longitudinal muscles), and the transverse muscle that divides the tongue (701) at the middle. The probe may be configured to contact the mucosa overlying one or more of the genioglossus (920) arising from the mental spine of the mandible (922) and the hyoid (924), and the palatoglossus (708) arising from the palatine aponeurosis of the soft palate (704).
The probe may be configured to contact the mucosa overlying the outer circular layer of the pharynx (902), including one or more of the superior (1102), middle (1104), and inferior (906) constrictor muscles. The superior constrictor muscle (1102) couples to the medial pterygoid plate, the pterygomandibular raphè, and the alveolar process. The middle constrictor muscle (1104) extends from the hyoid. The inferior constrictor muscle (1106) couples to the cricoid and thyroid cartilage. The probe may be configured to contact the mucosa overlying the thyroarytenoid muscle (e.g., vocalis) (802) coupled between the inner surface of the thyroid cartilage and the anterior surface of the arytenoid cartilage.
The probe may be configured to contact the mucosa overlying one or more of the tensor veli palatini muscle and levator veli palatini muscle where the tensor veli palatini is anterior-lateral to the levator veli palatini muscle. The tensor veli palatini muscle is coupled to the medial pterygoid plate of the sphenoid bone and the levator veli palatini muscle is coupled to the temporal bone. The probe may be configured to contact the mucosa overlying the inferior pharyngeal constrictor (e.g., cricopharyngeus) that arises from the sides of the cricoid and thyroid cartilage. The probe may be configured to contact the mucosa overlying the interarytenoideus (804) located in the posterior larynx. The probe may be configured to contact the mucosa overlying the cricoarytenoid muscle (e.g., posterior and lateral cricoarytenoid muscle) (806) located between the cricoid cartilage and arytenoid cartilage. The probe may be configured to contact the mucosa overlying the cricothyroid muscle (808) of the larynx. The cricothyroid muscle (808) is coupled to the anterolateral aspect of the cricoid and the inferior cornu and the lower lamina of the thyroid cartilage. The probe may be configured to contact the mucosa overlying the cricoarytenoid muscles (e.g., posterior and lateral cricoarytenoid muscle) (810) of the larynx that connects the cricoid cartilage and arytenoid cartilage.
In some variations, a sensor assembly may comprise a transnasal probe configured to contact and measure electrical activity of one or more muscle tissues such as the Eustachian tube (1002) that links the nasopharynx to the middle ear, superior constrictor (1004), and cervical spine (1006). In variations where a rigid sensor probe is used transnasally, the rigid sensor probe may be inserted through a patient's nostril and advanced toward one or more nasopharynx muscles to be measured. In other variations, a rigid sensor probe may be used with a visualization device such as a rigid endoscope to measure one or more nasopharynx muscles.
In variations where a flexible sensor probe is used transnasally, the flexible sensor probe may be inserted through a patient's nostril and advanced toward one or more nasopharynx muscles to be measured. In some other variations, a flexible sensor probe may be used with a visualization device such as a flexible fiber optic rhinolaryngoscope, flexible fiber optic bronchoscope, flexible fiber optic esophagoscope, and flexible gastroduodenoscope to measure one or more tissue surfaces including the nasopharynx, oropharynx, hypopharynx, larynx, esophagus (as described in detail herein), and GI tract. For example, the flexible sensor probe may be slidably advanced through a lumen of the flexible visualization device.
For example, the probe may be configured to contact the mucosa overlying one or more of the upper esophageal sphincter (UES) (e.g., cricopharyngeal part of the inferior pharyngeal constrictor) (1108) that surrounds an upper portion of the esophagus (1120) and lower esophageal sphincter (LES) (e.g., gastroesophageal sphincter) (1110) that surrounds the lower part of the esophagus (1120) at the junction between the esophagus (1120) and the stomach (1130, 1200). The probe may be configured to contact the mucosa overlying one or more of the gastroduodenal sphincter (e.g., pyloric sphincter) (1112, 1210) surrounding the gastroduodenal junction and the sphincter of Oddi (1220) located between the pancreas and duodenum (1202).
A conventional NEMG needle inserted into an upper and/or lower GI tract may increase the risk of perforation of the viscus and may lead to catastrophic complications related to viscus perforation of the esophagus, duodenum, gallbladder, pancreas, small bowel, large bowel, sigmoid colon, and rectum. In some variations, a sensor assembly may comprise a gastrointestinal probe configured to contact the mucosa overlying muscle tissue such as a lower esophageal sphincter, gastroduodenal juncture, gall bladder, pancreas, small and large intestine sigmoid colon, and rectum. The sensor assembly may comprise one or more flexible and rigid GI endoscopes. The gastrointestinal probe may be disposed in the endoscope using an endoscope port. One or more sensors of the GI probe may be configured to be located on a mucosal surface of the GI tract. In some variations, a distal end of a flexible GI probe may be oriented to be adjacent to a submucosal muscle of interest. For example, the probe may be configured to contact one or more of the lower esophageal sphincter, gastroduodenal sphincter, sphincter of Oddi and gastric tissue, as described in detail herein. In some variations, a rigid probe may slidably advance through a rigid scope such as a rigid esophagoscope, sigmoidoscope, or other operative rigid endoscope.
The EMG data generated from the gastrointestinal probe signal data may be used, in adult and pediatric populations, to evaluate one or more of dysphagia (including the pharyngeal muscles), cricopharyngeus, esophageal muscles, lower esophageal sphincter, pancreatic sphincter, bile duct sphincter, anal sphincter, Ogilvie syndrome, gastrointestinal neoplasm, gallstone ileus, intestinal adhesions causing obstruction, volvulus, intussusception, amyotrophic lateral sclerosis, Brown-Sequard syndrome, central cord syndrome, multiple sclerosis, Parkinson's disease, spina bifida, spinal cord injury, lesions and aging, and diabetes mellitus.
Conventionally, usage of NEMG in and around the eye is difficult to perform. For example, an awake patient may suffer from one or more of insertion pain, procedure fear, local trauma, and bleeding. During the procedure, the needle may need to be repositioned, making patient tolerance and diagnostic compliance even more difficult. A needle electrode further carries a higher risk of intraorbital complications that may lead to double vision, infections, hemorrhage, and/or blindness. General anesthesia may be used to reduce some of these issues, but the use of anesthesia adds complexity, cost, and other possible complications to the procedure. As a result, orbital NEMG is typically limited to specific operating room nerve monitoring conditions.
In some variations, a sensor assembly may comprise an orbital probe configured to contact muscle tissue such as one or more eye muscles such as a medial rectus, lateral rectus, superior oblique, inferior rectus, inferior oblique, and superior rectus. One or more sensors may be configured to be located topically on the eye to measure EMG activity of the extraocular muscles through the conjunctival membrane. In some variations, topical anesthesia may be applied to the conjunctiva and the orbital probe may be subsequently placed directly on the conjunctiva of the overlying muscle. The EMG data generated using the orbital probe signal data may be used to evaluate one or more of Battaglia Neri syndrome, dermatomyositis, diabetic neuropathy, encephalitis, meningitis, multiple sclerosis, myasthenia gravis, Parkinson's disease, subacute sclerosing pan encephalitis, tumor infiltration into muscle, Grave's disease, accommodative esotropia, Brown syndrome, strabismus, convergence insufficiency, dissociated vertical deviation, Duane syndrome, esotropia, exotropia, oculomotor apraxia, abnormal head position, conjugate gaze palsies, internuclear ophthalmoplegia, microvascular cranial nerve palsy, monocular elevation deficiency (double elevator palsy), palsies of the cranial nerves that control eye movement, progressive supranuclear palsy, and pseudo strabismus.
In some variations, a sensor assembly may comprise an endovascular probe configured to contact muscle tissue such as myocardium, aortic, mitral, pulmonic, tricuspid valves, and all endothelially lined vascular surfaces where adjacent muscle is anatomically known. One or more sensors may be configured to be located on an endothelial surface that anatomically correlates to a muscle such as a myocardium, heart valves, and chordae tendineae to measure EMG activity of those muscles. The EMG data generated using the endovascular probe signal data may be used to evaluate one or more of transient or chronic autonomic dysfunction related to cerebrovascular disease, myocardial infarction or areas of ischemic muscle tissue, valvular disease and muscle function, left ventricular dysfunction arrhythmia, degenerative brain disorders present with myocardial disease, degenerative neurological conditions, cardiomyopathy, neuromuscular disorders, mitochondrial myopathies, dystrophies, cardiac conduction defects, and renovascular disease. Conventional NEMG needle insertion may increase the risk of perforation of the viscus and may lead to catastrophic complications in the myocardium and vascular system.
In some variations, a sensor assembly may comprise an orthopedic probe configured to contact muscle directly during surgery in all open muscle operations or via a rigid probe within a synovial cavity of a joint. The sensor assembly may comprise a rigid endoscope placed within the joint during surgical procedures of the joint. One or more sensors may be configured to be located on muscles that traverse through or near a synovial surface such as the shoulder, hip, knee, elbow, ankle, and the like. The EMG data generated from the orthopedic probe signal data may be used, in adult and pediatric populations, to evaluate one or more of muscle activity in open and endoscopic joint surgery, shoulder girdle muscle assessment, hip and knee joint muscle assessment, and any body joint accessible via an open or endoscopic technique.
In some variations, a sensor assembly may comprise a urologic probe configured to contact muscle tissue such as one or more of a urethra, urethral sphincter, and bladder. The sensor assembly may comprise one or more flexible and rigid endoscopes (e.g., cystoscope) advanced using a urethra or suprapubic approach. Conventional NEMG needle insertion may increase the risk of perforation of the viscus and may lead to catastrophic complications in one or more of the urethra and bladder. The EMG data generated from the urologic probe signal data may be used, in adult and pediatric populations, to evaluate one or more of a bladder, spermatic cord, ureteropelvic junction, ureter, ureterovesical junction, prostate, testis, and epididymis conditions. For example, bladder conditions may include overactive bladder, interstitial cystitis, post radiation muscle injury bladder, internal and external urethral sphincter, and bladder neck contracture. Spermatic cord conditions may include pain syndromes associated with cremasteric muscle spasms, varicocele associated with infertility and pain syndromes, and congenital malformations (prenatal in utero-transvaginal). Ureteropelvic junction conditions may include ureteropelvic junction (UPJ) obstruction (e.g., scar, cross-vessel, overactive muscles). Ureter conditions may include mega ureter (e.g., functional, scar, obstruction), ureterectasis (e.g., functional, obstruction), and hydronephrosis (e.g., functional, obstruction). Ureterovesical junction (UVJ) conditions may include vesicoureteral reflux (VUR), overactive bladder (OAB), neurogenic bladder (with or without spinal cord injury), chronic obstructive uropathy, detrusor sphincter dyssynergia, urethral stricture (to check muscle/scar function versus just scar function), and interstitial cystitis. Prostate conditions may include prostatodynia and/or pain syndromes. Testis conditions may include cryptorchidism retractile testis (e.g., overactive cremasteric muscle, true cryptorchid), and verumontanum/ejaculatory duct opening (e.g., obstruction, functional). Epididymis conditions may include epidydimal dilation (e.g., obstruction, functional). Vas Deferens conditions may include vassal immobility syndromes.
In some variations, a sensor assembly may comprise a tympanic and/or transtympanic probe configured to be contact muscle tissue such as one or more of a stapedius, including round and oval window; cochlea, and labyrinth. The probe may be configured to access the middle ear. In some variations, a probe in contact with the tympanic membrane may permit evaluation of one or more of the tensor tympani, the oval and round window, facial nerve, cochlea, and labyrinth.
In some variations, the probe may be configured to intraoperatively monitor inner ear function for all middle ear, middle fossa, and neurosurgery where monitoring of the vestibular, cochlear, and/or facial nerve may be performed, such as with acoustic neuroma surgery and inner ear surgery. The EMG data generated from the tympanic/transtympanic probe signal data may be used, in adult and pediatric populations, to evaluate one or more of vertigo including vestibular neuronitis, vestibular migraine, Meniere's disease, BPPV, tinnitus, hearing loss from aging, noise, trauma, autoimmune disease, vascular disease, sudden sensorineural hearing loss, ototoxicity, vestibulotoxicity, trauma, and fractures of the temporal bone and skull.
As described herein, EMG data may be generated using the sensor probe assemblies as described herein. For example,
As described herein and shown in
Rise time is the duration of a rapid positive-negative deflection (e.g., from spike onset SpO to peak P) and may correspond to a distance of muscle fibers to the electrode. For example, a shorter rise time corresponds to a shorter distance between the muscle fibers and the electrode. Duration may correspond to the time from initial deflection to a final return to baseline (e.g., from onset O to end E). For example, normal MUAPs may have a duration between about 10 ms to about 13 ms, although this range may vary among different muscles. Duration may also correspond to an area of the motor unit. Amplitude may correspond to a maximal peak-to-peak amplitude of a main spike of the MUAP (e.g., from peak P to peak end PE). Amplitude generally corresponds to the action potentials of a set of muscle fibers within the motor unit that are in close proximity to the portion of the electrode in contact with tissue. Phase may correspond to the number of times the action potential crosses the baseline plus one. For example, the MUAP may be monophasic, biphasic, triphasic, or polyphasic. Normal potentials may have three or four phases. A turn may correspond to a potential reversal greater than about 50 μV that does not cross the baseline.
The sensor assemblies as described herein may be configured to elastically deform the tissue surface without penetrating or piercing the intact tissue surface (e.g., intact epithelial surface) while receiving signal data corresponding to EMG data of a motor unit action potential having a rise time of less than about 500 μs. For example, the sensor assemblies as described herein may be configured to receive signal data corresponding to EMG data of a motor unit action potential having a rise time of less than about 300 or 400 μs while maintaining the tissue surface in an intact or unbroken state, e.g. without requiring needle puncture or anatomical dissection to achieve access to the target musculature. In some variations, the sensor probes as described herein may be repositioned when EMG data indicates motor unit action potential rise times above 500 μs. Surface electrodes used for SEMG are not sensitive enough to generate EMG data with rise times of less than about 500 μs due to the large surface area of the surface electrode.
Although the foregoing implementations has, for the purposes of clarity and understanding, been described in some detail by of illustration and example, it will be apparent that certain changes and modifications may be practiced, and are intended to fall within the scope of the appended claims. Additionally, it should be understood that the components and characteristics of the devices described herein may be used in any combination, and the methods described herein may comprise all or a portion of the elements described herein. The description of certain elements or characteristics with respect to a specific figure are not intended to be limiting or nor should they be interpreted to suggest that the element cannot be used in combination with any of the other described elements.
This application claims the benefit of U.S. Provisional Application No. 62/515,364, filed Jun. 5, 2017, and titled “TRANSMEMBRANE SENSOR TO EVALUATE NEUROMUSCULAR FUNCTION,” which is hereby incorporated by reference in its entirety.
| Number | Date | Country | |
|---|---|---|---|
| 62515364 | Jun 2017 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 16619909 | Dec 2019 | US |
| Child | 18467345 | US |
