Multi-functional diagnostic measuring system for vertebrates

Abstract

A multi-functional system for measuring neurological functions in an animal is provided. The system includes a diagnostic measuring device including a power source. The system further includes one or more stimulators for applying an electrical stimulus to the animal and a plurality of amplifiers. A computing device is connected to the diagnostic measuring device via a connector cable, whereby data is collected after the electrical stimulus is applied to the animal and the data is sent by the connector to the computing device.

Description

Docket No. 103267-230001MULTI-FUNCTIONAL DIAGNOSTICMEASURING SYSTEM FOR VERTEBRATES

[0001] This application claims the benefit of U.S. Provisional Patent Application No. 63 / 684,565 filed on August 19, 2024, the disclosure of which is incorporated herein by reference.

[0002] This disclosure relates generally to diagnostic products for animals and, more particularly, to a multi-functional system for measuring reflexes in muscles to diagnose neurologic disorders or infections and diagnosing sensory and motor functions of neural pathways in the spinal cord and peripheral nerves in vertebrates.BACKGROUND OF THE INVENTION

[0003] It is well known that veterinarians have a number of different diagnostic tools and measuring devices to diagnose animals and, more particularly, vertebrates, i.e., animals with a vertebral column and a cranium for a number of disorders, ailments, injuries, and illnesses. Furthermore, it is known to monitor the brain and spinal cord functions during human surgical operations where the nervous system is at risk via an intraoperative neuromonitoring (I0NM) system. The I0NM system also include other modalities for the sensory system, brain activity monitoring, brain stem auditory responses where other applications in neurosurgery and orthopedic surgery evolved. The I0NM system is also applicable for diagnostic clinical neurophysiological assessment.

[0004] Around the beginning of the twenty-first century, transcranial electrical stimulation (TES) and peripherally evoked motor potentials (MEP) became approved by the Federal Drug Administration (FDA) and companies introduced TES as modality into their systems. However, the data processing was not ideal for use in the operating room. Moreover, to date these systems offer extremely limited possibilities to diagnose neurological issues in vertebrates, such as ataxic horses.

[0005] Accordingly, there is a need for a multi-functional diagnostic measuring system utilizing a diagnostic device for measuring sensory and motor functions of nerve pathways in the spinal cord and peripheral nerves in patients, namely, vertebrate animals such as horses.SUMMARY OF THE INVENTION

[0006] In accordance with one aspect of the disclosure, a multi-functional system for measuring neurological functions in an animal is provided. The system includes a diagnostic measuring device including a power source. The system further includes one or more stimulators for applying an electrical stimulus to the animal and a plurality of amplifiers. A computing device is connected to the diagnostic measuring device via a connector cable, whereby data is collected after the electrical stimulus is applied to the animal and the data is sent by the connector to the computing device.

[0007] In one embodiment, the one or more stimulators may be a transcranial electrical stimulator. The one or more stimulators may be at least one peripheral stimulator. The one or more stimulators may be three stimulators, wherein a first stimulator is a transcranial electrical stimulator, a second stimulator is a first peripheral stimulator, and a second peripheral stimulator. Each of the plurality of amplifiers may be a physiological amplifier, wherein each of the plurality of amplifiers corresponds to a separate physiological measurement channel. The power source may be a battery. The battery may be a lithium ion battery. The lithium ion battery may be rechargeable. The data may be transcranial and peripherally evoked motor potentials (MEP). The data may be spontaneous and triggered EMG activity, reflex activity, evoked sensory potentials (SEP), and electro encephalographic (EEG) activity. The connector cable may be a USB cable. The computing device may be a mobile computing device. The animal may be a vertebrate. The vertebrate may be a horse.

[0008] In accordance with another aspect of the disclosure, a diagnostic measuring device for diagnosing neurologic disorders or sensory and motor functions of nerve pathways in a horse via one or more electrodes is provided. The diagnostic measuring device includes a housing and a tray configured to slide in and out of the housing for receiving a removable power source. The diagnostic measuring device further includes at least two electric stimulators, aplurality of physiological amplifiers, and a connector cable connected to a computing device such that data collected from the horse is stored and viewable on the computing device.

[0009] In one embodiment, the housing may be made of a rigid material, such as plastic. A first side of the device may have at least two indicator lights, wherein a first of the at least two indicator lights is a battery charge indicator and a second of the at least two indicator lights is a power on / off indicator. Each of the plurality of physiological amplifiers may have a positive input and a negative input. The number of the plurality of physiological amplifiers may be 4, 6, 8 or 10. Each of the plurality of physiological amplifiers controls a gain setting of a corresponding channel range. The corresponding channel range is selectable at ±5 mV, ±10 mV, ±20 mV, ±50 mV, and ±100 mV.

[0010] In another embodiment, the at least two electric stimulators may be a transcranial electrical stimulator, a first peripheral stimulator, and a second peripheral stimulator. Each of the at least two electric stimulators may have a positive input and a negative input. Each of the at least two electric stimulators may be a constant current stimulator. Each of the at least two electric stimulators may have a pulse shape of a true square wave. Each of the at least two electric stimulators may have a polarity in a biphasic mode or a monophasic mode. Each of the at least two electric stimulators may be connected to a stimulator trigger. The second side of the device may have a power on / off switch and a stimulator voltage supply charging indicator.

[0011] In accordance with yet another aspect of the disclosure, a method for measuring reflexes in muscles of an animal to diagnose neurological disorders, localize a location and extent of lesions in a spinal cord and / or a brain of the animal is provided. The method includes the following steps: (1) providing a multi-functional diagnostic measuring device; (2) delivering an electric stimulation to a desired area of the animal via electrodes connected to the device; (3) capturing a plurality of elicited potentials created by the electric stimulation to the desired area of the animal; (4) turning the plurality of elicited potentials into a corresponding plurality of waveforms; (5) monitoring the corresponding plurality of waveforms in real-time; and (6) diagnosing a particular disorder or the location and extent of lesions in the spinal cord and / or brain of the animal based on real-time monitoring, digitally stored data and subsequent off-line retrieval, analysis and interpretation for a diagnostic conclusion.

[0012] In one embodiment, the multi-functional diagnostic device includes a housing, a removable power source, at least two electric stimulators, a plurality of physiological amplifiers and a connector cable connected to a computing device. The monitoring step may be performed on a computing device.BRIEF DESCRIPTION OF THE DRAWINGS

[0013] The accompanying drawings incorporated in and forming a part of the specification, illustrate several aspects of this disclosure, and together with the description serve to explain the principles of the disclosure. In the drawings:

[0014] Figure 1 is a front perspective view of a diagnostic measuring device forming one aspect of this disclosure;

[0015] Figure 2 is a rear perspective view of the diagnostic measuring device forming one aspect of this disclosure;

[0016] Figure 3 is an exploded perspective view of a USB connector connecting to the diagnostic measuring device forming one aspect of this disclosure;

[0017] Figure 4 is an exploded perspective view of a battery tray in an extended position from the diagnostic measuring device forming one aspect of this disclosure;

[0018] Figure 5 illustrates stimulation and recording with and without the artifact killing principle for the diagnostic measuring device forming one aspect of this disclosure;

[0019] Figure 6 illustrates measurement of the stimulation artifacts at a multi-pulse stimulation depicting the difference between monophasic and biphasic pulses of a combined stimulation for the diagnostic measuring device forming one aspect of this disclosure; and

[0020] Figure 7 is a block schematic diagram of the electronic circuits for the diagnostic measuring device forming one aspect of this disclosure.Detailed Description

[0021] In the following detailed description, reference is made to the accompanying drawings that form a part hereof, and in which is shown by way of illustration, specific embodiments in which the invention may be practiced. These embodiments are described in sufficient detail to enable those skilled in the art to practice the embodiments and like numeralsrepresent like details in the various figures. Also, it is to be understood that other embodiments may be utilized and that process or other changes may be made without departing from the scope of the disclosure. The following detailed description is not to be taken in a limiting sense, and the scope of the invention is defined only by the appended claims and their equivalents. In accordance with the disclosure, a multi-functional diagnostic measuring system utilizing a diagnostic device for measuring sensory and motor functions of nerve pathways in the spinal cord and peripheral nerves in vertebrates, such as horses is hereinafter described.

[0022] Reference is now made to Figures 1-7, which illustrate the system known as the EQUTDSTIM system (ES) 10 that is designed for both diagnostic and scientific applications. The EQUIDSTIM system 10 may be used to measure transcranial and peripherally evoked motor potentials (MEP), spontaneous and triggered electromyography (EMG) activity, reflex activity, encephalographic brain activity (EEG) and evoked sensory potentials (SEP) of the brain and sensory nerves of the patient. Specifically, the EQUIDSTIM system 10 utilizes electrodes to stimulate and record biological potentials of the peripheral and central nervous system. The qualified physician hooks up the electrodes over the selected area of the patient or animal and delivers electrical stimulation to the desired area and other electrodes may be used to capture elicited potentials or otherwise measure spontaneous generated electrical activity from the tissues with the selected channels, which may be turned into waveforms, which may be monitored in real-time, digitally stored data and subsequent off-line retrieval, analysis and interpretation for a diagnostic conclusion. The EQUIDSTIM system 10 is configured to meet the highly demanding requirements for extensive neurological applications in electrically hostile environments of various veterinary or medical treatment rooms as well as other environments without the presence of an AC mains grid. The EQUIDSTIM system 10 may be used for neurophysiological diagnostics of the motor functions of the nervous systems to provide equine medical practitioners (veterinarians) with information to assess the neurological status of the patient, such as a horse.

[0023] As perhaps best shown in Figures 1 and 2, the EQUIDSTIM system 10 includes a diagnostic measuring device 20 having certain design-specific features including both hardware and software components for measuring and diagnosing transcranial and MEP, spontaneous and triggered EMG activity, reflex activity, and SEP. Typically, the hardware component for the device 20 is equipped for modalities for motor and sensory evoked potentials and nervepotentials, transcranial stimulation techniques for motor aroused potentials for assessing dysfunctions in axonal conduction along corticospinal pathways and peripheral nerves, EMG and various peripheral stimulation techniques for assessing the peripheral motor and sensory nerve conduction and measurement of evoked cortical sensory potentials. Furthermore, the modalities may be available in specific software modules. The diagnostic measuring device 20 is conceptually similar to commercial equipment used for I0NM during human surgical operations wherein the nervous system is at risk.

[0024] As shown in Figure 1, the front side of the device 20 includes two indicator lights: a battery low indicator 30 and a power on indicator 40. The device 20 also includes a plurality of physiological amplifiers 300, each amplifier having a positive input 50 and a negative input 60. There are also ground inputs 70. In the illustrated embodiment, there are ten physiological amplifiers, but as discussed in more detail below, it should be appreciated that the number of physiological amplifiers may be varied. The physiological amplifiers control the gain setting for the channel input range and selectable ranges are ±5 mV, ±10 mV, ±20 mV, ±50 mV, and ±100 mV. The sample frequency is 25kHz / channel and the sweep length is MEP: 200ms (5000 samples / channel) and free running: maximum 10- 1000ms.

[0025] Furthermore, the device 20 includes may include up to three electric stimulators: a transcranial electrical stimulator (TES) 400 having a positive output 80 and a negative output 90; a first peripheral stimulator (STIM1) 500 having a positive output 100 and a negative output 110; and a second peripheral stimulator (STIM2) 600 having a positive output 120 and a negative output 130.

[0026] The electric stimulators are built into the device 20 and are constant current stimulators as one common stimulator which by the relays 400, 500 and 600 can be connected via software programmable microcontroller to the output connecting tough-proof plugs to the TES 400, STIM1 500 or STIM2 600 stimulators. Similar to prior TES stimulators, which housed constant voltage as well as a constant current stimulator, the heart of the stimulator is a bridge circuit by which monophasic and biphasic pulses can be generated. The timing of the pulse sequences is now brought under control of the processor of the ADC / DA unit and, thus, fully programmable. The transcranial electrical stimulator (TES) is a constant current stimulator having a true square wave pulse shape. The polarity may be biphasic (2 alternating polarityphases) or monophasic (1 phase) mode. The biphasic transition interval may be 20 ps. The pulse width is selectable as 25, 50, 75 and 100 ps for fast charge delivery clinical application and 200, 500, and 1000 ps is allowed only for scientific use. The interpulse interval (IPI) minimum in monophasic mode is PW + 20 ps and 2PW + 40 ps in biphasic mode, while the maximum in either mode is 10 ms. The number of pulses / train is 1-5 ppt, the intensity is 0-1000 mA and accuracy is 1 mA.

[0027] The first and second peripheral stimulators are constant current stimulators delivering a true square wave pulse shape. The polarity may be biphasic (2 phases) or monophasic (1 phase) mode. The biphasic transition interval may be 20 ps. The pulse width is selectable as 25, 50, 75, 100, 200, 500, and 1000 ps. The interpulse interval (IPI) minimum in monophasic mode is PW + 20 ps and 2PW + 40 ps in biphasic mode, while the maximum in either mode is 10 ms. The number of pulses / train is 1-5 ppt, the intensity is 0-200 mA and accuracy is 1 mA.

[0028] Turning to Figure 2, the back side of the device 20 includes a power on / off switch 140 and a stimulator voltage supply charging indicator 150. The device 20 further includes a power source container 160 for housing a power source 170 (not shown in Figure 2). The device 20 also includes a stimulator trigger having a trigger out port 180 and a trigger in port 190. Finally, the device 20 includes a USB connector port 200 for connecting the device to a computing device 210 (not shown in Figure 2) via a USB cable 220 (also not shown in Figure 2).

[0029] Advantageously, the diagnostic measuring device 20 made be made of an impactresistant material, such that it can withstand the rigors of in field use. For example, in one particular embodiment, the device 20 may be made of a rigid plastic material. Test leads are preferably relatively short to make the device less susceptible to interference. With reference to Figure 3, the length of the USB cable 220 connecting the diagnostic measuring device 20 to a computing unit 210 (as shown in Figure 3) may be relatively long, while EMG extension cables can be missed. The computing unit 210 may be a mobile computing unit, such as a laptop, notebook, or tablet or it may be a desktop computing unit.

[0030] The power source 170 for the system may a rechargeable Lithium ion battery such that it can be used in the field as a stand-alone piece of equipment and not tied to a wired power source. It may be turned on by an on / off switch 171. As shown in Figure 4, the rechargeablebattery is positioned within the power source container 160 which takes the form of a compartment or tray that conveniently slides in and out of the housing of the diagnostic measuring device 20. In that way, the rechargeable battery may be easily removed from device for recharging.

[0031] The stimulator trigger may be used separately from the EQUIDSTIM system such that is integrated in the design in the housing of the diagnostic measuring device 20. Importantly, the stimulator trigger remains isolated from all circuits and gets it power from a DC-DC converter 176, which, in turn, is connected to the battery of the system. The stimulator trigger consists of an oscillator circuit with step-up transformer for generating the high voltage supply to a buffer capacitor. A processor of the ADC / DA unit is programmed such that the oscillator is only active outside the signal data sampling, which prevents signal noise in the measuring channels from the oscillator.

[0032] In addition, this creates the advantage of not requiring electrical safety requirement for current leakage that is required when the power source is separate from the device as in prior devices. As perhaps best shown in Figure 7, the design includes fully isolated electronic circuits for stimulation, a plurality of physiological measurement channels, processors for embedded control of functions, data processing, and communication with the computing device via the USB cable. In case the computing device is connected with a defective charger by which the mains AC voltage under a fault condition gets galvanic connected with the USB, the isolated design still guarantees leakage currents below 10 micro-Amp to the patient ground which is below the strictest medical safety requirements. The EQUIDSTIM system 10 is intended for use at a small distance from the patient or horse.

[0033] The EQUIDSTIM system 10 includes a graphical user interface for entering demographic and research data, parameter selection and elaboration of graphically displayed measurement data and digital storage thereof on the computing device. The A / D conversion is housed in the hardware of the device 20. Although the measuring system is rechargeable and not connected to the mains, isolation amplifiers to the USB connection of a notebook and stimulation circuits ensure minimal interference and leakage currents at the patient’s location. The settings of the stimulation parameters are limited to values that can be considered electrically safe. The physiological amplifiers combined with digital signal processing are used to ensure high-qualityrecorded data. The system includes multiple digital signal processors and microcontrollers to improve product flexibility, response time, and patient safety. Again, all patient connections are protected against interference.

[0034] Importantly, the high impedance of a current stimulator is only applicable during the stimulation pulses. Outside of that window, low impedance is made by an active short circuit. In other words, outside the monophasic or biphasic pulses, the output is given a low impedance, like in a constant voltage stimulator, by an active short circuit. As a result, the charge that is injected into the vertebrate’s tissue during the stimulation pulses is quickly drained so that the stimulation artifacts disappear quickly. In common designs of current stimulators where the output impedance remains high, the artifacts last a much longer time. The fastdraining principle is applied in both the transcranial and peripheral stimulators. An optimal effect is obtained when using biphasic instead of monophasic pulses in combination with the fast residual charge drainage method.

[0035] This feature of the transition from the high to low-impedance state makes it possible to stimulate a muscle by switching the connection between the muscle electrodes and stimulator after stimulation over into a connection between the muscle electrodes and measuring channel while the stimulator is uncoupled. This is done by quick switching relays. The instant of the switching is completed a short time interval after completion of the stimulation pulses: Tstim. This extra time permits a fast unloading of the remaining injected charge in the tissue in the low impedance state. This set-up makes it possible to measure reflexes in the same muscle that is being stimulated. A stimulation-recording cycle is divided into three time windows: (1) Tstim: electrodes are connected with the current stimulator; (2) TtranS: electrodes are neither connected with the stimulator nor amplifier; and (3) TmeaS: electrodes are connected to the physiological amplifier.

[0036] Turning to Figure 5, it is an impression of the expectation how the Artifact Killing Principle or effect works out in practice. As shown in Figure 5, the stimulation and recording without (panel A: no additional time after the stimulus pulse for unloading of the injected charge) and with the Artifact Killing Principle or effect (Panel B: extra time available for unloading) in a set-up with combined electrodes in a pre-contracted muscle causing background noise. Due to the short-cutting in the unloading phase, the signal follows a straight line. Thetransition phase between the connection with the stimulator and physiological amplifier is not considered. This example illustrates the Artifact Killing Principle or effect in the muscle at subsequent stimulation, injected charge unloading and measurement.

[0037] With reference to Figure 6, it demonstrates the actual effect in practice of a simultaneous measurement in a human subject on a slightly contracted agonist / antagonist muscle pair. In this case, the extensor in the forearm is considered the agonist and the flexor is considered the antagonist. The extensor signals are measured with the combined stimulationrecording set-up sharing one surface electrode pair. The flexor signal is a continuous during the stimulation phase uninterrupted recording. The surface electrodes of the agonist are connected to the hybrid stimulation-measurement channel and those of the antagonist to a single continuous present measurement channel without the stimulation capability. Panel A shows the muscle signal of the agonist (the line marked 21.0 mV) of the hybrid channel during initial stimulation with three monophasic pulses (three 10 mA pulses / train pulse width: 100 ps / phase) in the measurement sequence as well as that of the antagonist (the line marked -20.5 mV) of the continuous measurement channel. In this example, Tstimmarks the stimulation phase and Tmeas is the measurement phase. The transition between the two phases reserved for the switching of the switching contacts of the relay is marked by Ttrans. This concerns the open connections where the electrodes of the muscle are no longer connected to the stimulator and not yet to the input of the physiological amplifier. In panel C, the amplitude of the agonist’s signal (the line that drops sharply) is magnified so that the background activity of the muscle becomes visible while the time axis is extended 5 times from 40 ms to 200 ms, i.e. it shows the background EMG activity of the precontracted muscles at a larger amplification.

[0038] In panel B, the muscle signals of agonist (the line marked -2.7 mV) and antagonist (the line marked 9.30 mV) are displayed in the same way when stimulated with 3 biphasic pulses (three 10 mA pulses / train pulse width: 100 ps / phase). The advantage of biphasic stimulation becomes visible with a marked reduction of the stimulation artifact. This is explained by the neutralizing effect of the immediate drainage by the second phase of the charge injected into the tissue in the first phase. After the three pulses, the discharge is continued by subsequent activation of the short-circuiting circuit of the stimulator (essential and novel part in the design). Panel D also shows the background EMG activity of the precontracted muscles at a largeramplification and five-fold enlarged time scale and the antagonist link is the one that decreases sharply).

[0039] It is indeed shown that smallest artifacts arise at biphasic stimulation as explained by the absence of active charge pulling in the compensatory biphasic pulse. The antagonist muscle signal shows a build-up effect of the residual charge in both the bi- and monophase pulse series. The shortcutting effect at the agonist electrodes exerts also some influence on a distance and it is noted that the artifact of the antagonist is also attenuated by partial unloading of the residual charge. The difference between the artifacts from monophasic and biphasic stimulation are indicated in the uninterrupted responses after the stimulation pulses of the antagonist where amplitude magnitudes, when comparing their absolute values, are reduced by -50% from abs(- 20.5) = 20.5 mV to 9.3 mV. The difference between the artifacts from monophasic and biphasic stimulation are evident when comparing the signal amplitudes of the agonist of the hybrid simulation-measuring channel where the artifact killing principle shows a more effective reduction of 88% from 21.0 mV to abs(-2.7) = 2.7 mV.

[0040] Turning to Figure 7, a block schematic overview of the electronic circuits of the EQUTDSTIM system 10 is illustrated. The system is divided into four electrically separated sections (A, B, C, and D) which keeps the patient connections fully isolated from the external connections and the battery module.

[0041] Section A contains the battery 170 (a Lithium ion battery in this example) the stimulator circuitry for the three stimulators 400, 500, and 600, which is connected to a high voltage generator 172 and a microcontroller 700. The microcontroller provides complete control of the three stimulators via the high-voltage voltage generator 172, which is electrically connected to the stimulators via H-bridge current source 173. The voltage generator 172 (400V) is necessary for current stimulator. The H-bridge current source 173 Constant current stimulation circuitry by which biphasic pulses are generated by a C-MOS bridge (monophasic stimulation pulses can be generated as well). Element 12 is DC voltage regulator for the microcontroller 700 and the DC / DC isolated converter 176.

[0042] The microcontroller 700 is connected with the current source 173 via Digital Analog Converter (DAC) 11. The DAC 11 is used for the setting of the pulse current intensity, i.e., 0-1000 mA for TES and 0-200 mA for the peripheral stimulators. The microcontroller 700further provides communication with the trigger inputs and outputs, the selection of the stimulation outputs, the high (for TES) and low (for peripheral stimulation) current intensity stimulation configuration. This includes the selection of four combined stimulationmeasurements channels, permitting the activation of the artifact killing method and communication with a data acquisition module 800.

[0043] Section B contains the isolated circuits for USB connection to the computing device 210, including USB 174 and USB isolator 175, which in turn are connected to the data acquisition module 800.

[0044] Section C contains the data acquisition module 800 and up to ten physiological amplifiers 300, which are all powered by the battery 170 via a pair of DC-DC optic isolated converters 176. The DC / DC converters power the isolated parts, i.e., trigger connections and stimulator. The physiological amplifiers 300 are connected to the data acquisition module 800 via Analog in 188. The physiological amplifiers 300 are connected to the microcontroller 700 via optocoupler 183, while the data acquisition module 800 is connected to the microcontroller via optocouplers 181 and 182. Specifically, optocouplers 181 and 182 provide the digital signal transmission between the data acquisition module 800 and the microcontroller 700. Optocoupler 181 is concerned with the data stream from the microcontroller 700 to the data acquisition module 800, while optocoupler 182 is concerned with the data stream from the data acquisition module 800 to the microcontroller 700. Optocoupler 183 is the one-way data transfer from the microcontroller 700 to the relays that connect the channels to either the stimulator output or to inputs of the physiological amplifiers 300. The stimulator output is connected to only one of the first four hybrid channels while the other channels remain connected to the physiological amplifiers.

[0045] Aside from the channel selection, the microcontroller 700 also controls: (1) the creation and timing of the monophasic or biphasic pulses which implies the pulse sequencing, pulse duration per phase; (2) the setting of analogue value of the current intensity (pulse amplitude) of the created pulses; (3) the transition from the high impedance state during current stimulation to the short cutting (low output impedance) state of the stimulator, which is intended to drain the injected current in the stimulated tissue during the unloading phase; and (4) theinterval timings of “stimulator connected” (Figure 5) or “Tstim” (Figure 6) and “electrodes connected to amplifier” (Figure 5) or “Tmeas” (Figure 6).

[0046] Section D is the isolated module for the separate trigger input 184 and trigger output 185 connections, which are connected to the microcontroller 700 and another DC-DC converter 176i, respectively. Trigger input 184 is connected to the microcontroller 700 via optocoupler 186, while trigger output 154 is connected to the microcontroller 700 via optocoupler 187.

[0047] It should be appreciated that the number of physiological measurement channels may vary, but is typically four, six, eight, or ten channels corresponding to the number of physiological amplifiers. By utilizing a number of channels, the same measuring electrodes may be used to measure electrically stimulated and generated responses while maintaining a high electrical separation. As a result, it is possible to measure reflexes in the same muscle where they are triggered. To do this, the unique artifact-killing properties of the current stimulators are used. It should be emphasized that reflex measurements have an important diagnostic value, especially for horses.

[0048] As noted above, the EQUIDSTIM system 10 also incorporates a software component, which allows the concept to be customized for equine veterinary use, such as for diagnosis in ataxic horses. The software component may be an application for a mobile device or downloadable program stored on a hard drive. The user interface is the platform for accessing various functions: (1) Patient - patient portal; (2) Setup - preparing the system for measurements; (3) Impedance - impedance measurement of recording electrodes (This is also a feature incorporated in the hardware of the system that makes it possible to simultaneous measure the impedances over either all - inputs or all + inputs of all ten physiological amplifiers); (4) Signal Check - signal check recording electrodes; (5) Measurements - access to recorded data, graphic display, new measurements, and reporting; (6) System - updating muscle names lists and set path for data; (7) Import - import data from another EQUIDSTIM system; and (8) Battery - battery level check.

[0049] The EQUIDSTIM system 10 may be further elaborated with equine neurologists, including: (1) measurement procedure - creation of graphic landscape MEPs with increasing stimulation intensities; (2) discrimination of latencies from extracranial reflexes and intracranialresponses; (3) automizing analyzing window settings, which is important for automated creation of Amplitude-Parameter curves like in the IONM system - the parameters relate to intensity, pulse width, interpulse interval, and intertrain interval; (4) elaboration of sensory evoked potentials for discrimination of the cerebellar, central or peripheral (proprioceptive) cause ataxia; and (5) patient data - demographics, measured samples, etc. in spreadsheets and the like. Importantly, patient data and stimulation parameters may be stored simultaneously with each elicit response, along with entered comments, so that they can be traced and labeled afterwards in graphical presentations of the measurements and printed in different formats. The EQUIDSTIM system 10 may include determining whether reflexes have a diagnostic meaning in horses.

[0050] In use, the basic elements of the system are the computing device which is connected with an internal processing circuit (via the USB cable) that replaces the old ADC / DA converter which performs the conversion of analogue signals from the measurement channels, programming of the gain, multiplexing, digitized signal handling and data transmission to the notebook and several control functions of the stimulators, etc. The physiological amplifiers and electrical stimulators may be electrical isolated from each other by opto-isolators and relays.

[0051] Other advantages of the multi-functional system include preventing saturation effects of amplifiers by permitting closer distances between stimulation and recording electrodes. Importantly, it is possible to measure reflexes in the same muscle that is being stimulated. In one particular embodiment, simultaneous segmental spread reflex measurements to other muscle groups are possible with up to ten channels utilized in the EQUIDSTIM system. Simultaneous measured responses are more accurate since test-to-test variability is excluded while also shortening the assessment time by eliminating the need for repeating measurements. Combined stimulation-recording possibility available in multiple channels. Importantly, there is no need to place additional stimulation electrodes because of the shared use of a single electrode pairs for stimulation and recording: saves time for set-up and assessment, less stressful for the animal, no extra costs for stimulation electrodes.

[0052] The foregoing descriptions of various embodiments have been presented for purposes of illustration and description. These descriptions are not intended to be exhaustive or to limit the invention to the precise forms disclosed. The embodiments described provide thebest illustration of the inventive principles and their practical applications to thereby enable one of ordinary skill in the art to utilize the disclosure in various embodiments and with various modifications as are suited to the particular use contemplated.

Claims

What is Claimed:

1. A multi-functional system for measuring neurological functions in an animal, comprising: a diagnostic measuring device including a power source; one or more stimulators for applying an electrical stimulus to the animal; a plurality of amplifiers; and a computing device connected to the diagnostic measuring device via a connector cable, whereby a data is collected after the electrical stimulus is applied to the animal, the data is sent by the connector to the computing device.

2. The system according to claim 1, wherein the one or more stimulators is a transcranial electrical stimulator.

3. The system according to claim 1, wherein the one or more stimulators is at least one peripheral stimulator.

4. The system according to claim 1, wherein the one or more stimulators is three stimulators.

5. The system according to claim 4, wherein a first stimulator is a transcranial electrical stimulator.

6. The system according to claim 5, wherein a second stimulator is a first peripheral stimulator.

7. The system according to claim 6, wherein the third stimulator is a second peripheral stimulator.

8. The system according to claim 1, wherein each of the plurality of amplifiers is a physiological amplifier.

9. The system according to claim 8, wherein each of the plurality of amplifiers corresponds to a separate physiological measurement channel.

10. The system according to claim 1, wherein the power source is a battery.

11. The system according to claim 10, wherein the battery is a lithium ion battery.

12. The system according to claim 1 1, wherein the lithium ion battery is rechargeable.

13. The system according to claim 1, wherein the data is transcranial and peripherally evoked motor potentials (MEP).

14. The system according to claim 1, wherein the data is spontaneous and triggered EMG activity, reflex activity, evoked sensory potentials (SEP) and electro encephalographic (EEG) activity.

15. The system according to claim 1, wherein the connector cable is a USB cable.

16. The system according to claim 1, wherein the computing device is a mobile computing device.

17. The system according to claim 1, wherein the animal is a vertebrate.

18. The system according to claim 17, wherein the vertebrate is a horse.

19. A diagnostic measuring device for diagnosing neurologic disorders or sensory and motor functions of axonal pathways in a horse via one or more electrodes, comprising:a housing; a tray configured to slide in and out of the housing for receiving a removable power source; at least two electric stimulators; a plurality of physiological amplifiers; and a connector cable connected to a computing device such that data collected from the horse is stored and viewable on the computing device.

20. The device according to claim 19, wherein the housing is made of a rigid material.

21. The device according to claim 20, wherein the rigid material is plastic.

22. The device according to claim 19, wherein a first side of the device has at least two indicator lights.

23. The device according to claim 22, wherein a first of the at least two indicator lights is a battery charge indicator.

24. The device according to claim 23, wherein a second of the at least two indicator lights is a power on / off indicator.

25. The device according to claim 19, wherein each of the plurality of physiological amplifiers has a positive input and a negative input.

26. The device according to claim 19, wherein a number of the plurality of physiological amplifiers is 4.

27. The device according to claim 19, wherein a number the plurality of physiological amplifiers is 6.

28. The device according to claim 19, wherein a number the plurality of physiological amplifiers is 8.

29. The device according to claim 19, wherein a number the plurality of physiological amplifiers is 10.

30. The device according to claim 19, wherein each of the plurality of physiological amplifiers controls a gain setting of a corresponding channel range.

31. The device according to claim 30, wherein the corresponding channel range is selectable at ±5 mV, ±10 mV, ±20 mV, ±50 mV, and ±100 mV.

32. The device according to claim 19, wherein the at least two electric stimulators are a transcranial electrical stimulator, a first peripheral stimulator, and a second peripheral stimulator.

33. The device according to claim 32, wherein each of the at least two electric stimulators have a positive input and a negative input.

34. The device according to claim 32, wherein each of the at least two electric stimulators are a constant current stimulator.

35. The device according to claim 34, wherein each of the at least two electric stimulators have a pulse shape of a true square wave.

36. The device according to claim 35, wherein each of the at least two electric stimulators have a polarity in a biphasic mode.

37. The device according to claim 35, wherein each of the at least two electric stimulators have a polarity in a monophasic mode.

38. The device according to claim 32, wherein each of the at least two electric stimulators are connected to a stimulator trigger.

39. The device according to claim 19, wherein a second side of the device has a power on / off switch.

40. The device according to claim 39, wherein the second side of the device has a stimulator voltage supply charging indicator.

41. A method for measuring reflexes in muscles of an animal to diagnose neurological disorders, localize a location and extent of lesions in a spinal cord and / or a brain of the animal comprising: providing a multi-functional diagnostic measuring device; delivering an electric stimulation to a desired area of the animal via electrodes connected to the device; capturing a plurality of elicited potentials created by the electric stimulation to the desired area of the animal; turning the plurality of elicited potentials into a corresponding plurality of waveforms; monitoring the corresponding plurality of waveforms in real-time; and diagnosing a particular disorder or the location and extent of lesions in the spinal cord and / or brain of the animal based on real-time monitoring, digitally stored data and subsequent off-line retrieval, analysis and interpretation for a diagnostic conclusion.

42. The method according to claim 41, wherein the multi-functional diagnostic device includes a housing, a removable power source, at least two electric stimulators, a plurality of physiological amplifiers and a connector cable connected to a computing device.

43. The method according to claim 41, wherein the monitoring and analyzing steps are performed on a computing device.

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