Modular Neuronet-VII Intraoperative Neurophysiological Monitoring System

FIELD OF THE INVENTION

The present invention relates to intraoperative neurophysiological monitoring (IONM) systems and, in particular, to a modular IONM system that includes a conceptually unique system architecture comprising serial pods that allow for real-time collection of data and for software which allows for communications with a remote attending physician to allow this information to be used to significantly reduce patient morbidity.

BACKGROUND OF THE INVENTION

Intraoperative neurophysiological monitoring is currently used in thousands of surgical procedures every year. The first use of IONM dates back to the 1930s, when direct stimulation of the brain was used to identify the motor cortex of patients with epilepsy undergoing intracranial surgery. Later on, it was the introduction of new monitoring techniques and commercial IONM machines in the early 1980s that allowed for the widespread adaptation of this technique.

Technological advances in the last twenty years have allowed monitoring techniques to continually evolve. The enhanced computational power and widespread availability of computer networks and communication systems has allowed IONM data to be acquired in greater and more relevant amounts and for the interpretation of this data to be performed from remote sites in real-time. This has made IONM more relevant and accessible in the last two decades.

Currently, however, available IONM systems present with several important drawbacks, namely: (1) placement of the system electronics in centralized enclosures rather than as distributed modular components limiting the flexibility and increasing the cost of these systems; (2) the use of blocking capacitors to remove DC drift, which has the undesired effect of removing very low signal frequencies; (3) inability to remove the electrical noise produced by the high frequencies and voltages used in electrocautery which prevents the IONM systems from acquiring data during the times when cautery is being used; (4) lack of a method to suppress excess common noise which obscures the signals of interest for extended periods of time; (5) a limited number of data channels not allowing all data of interest to be acquired; (6) a limited amount of data storage which limits the amount of acquired data which may be stored during a particular procedure; (7) limitations in the methods for presenting stimulation data; and (8) limitations in the methods for presenting data remotely and the bi-directional communication channels supporting the interpretation of these data. There is an important need, therefore, for an IONM system that not only addresses these shortcomings but improves the state of the art of IONM systems to an advanced level of functionality, versatility and performance.

SUMMARY OF THE INVENTION

The present invention fulfills this need by providing a unique intraoperative neurophysiological monitoring (IONM) system, referred to as “NeuroNet-VII” (“the NeuroNet-VII System” or “the System”), which is the first IONM system designed with a system architecture comprising serial modules. This conceptually unique architecture includes a number of novel features and utilizes novel engineering approaches to address and overcome the drawbacks enumerated above. The nature of the module architecture makes the system highly modular as opposed to all other prior art systems which tend to place all the components in a limited number of centralized enclosures.

The modular architecture of the present invention is of value to users for several reasons: (1) the user only needs to buy the modules that are needed; (2) a module in need of repair will not disable the entire system but may be easily individually replaced; and (3) advances in hardware designs may be implemented for a specific module without requiring replacement of an entire system.

The NeuroNet-VII system of the present invention utilizes distributed computer technology to meet four objectives: (1) the acquisition and processing of multi-modality data; (2) the integration of these data into various display formats suitable for specific applications; (3) the management of data communication between the serial modules; and (4) the presentation of the various data types in such a way as to allow multiple individuals at various distributed sites to consult in meaningful ways concerning the shared data as well as to interpret the shared data.

The NeuroNet-VII system provides several unique features: (1) true multi-modality simultaneous data acquisition supporting all data types useful in the operating room, diagnostic laboratories, intensive care unit and epilepsy monitoring unit; (2) extensive intra-and internet communication facilities supporting data, text, video and audio multi-directional distribution; (3) elegant graphical user interfaces providing ease of use and efficient data presentation; and (4) a set of signal processing and data analysis tools.

The NeuroNet-VII system acquires, processes and displays physiological data from selected areas of the central and peripheral nervous system essentially in a simultaneous fashion. This allows for real-time assessment of data, both locally and remotely, and for communications with a remote attending physician so that this information can be used to reduce morbidity.

The NeuroNet-VII system is designed to support intra-operative neurophysiological monitoring, intensive care unit (ICU) neurophysiological monitoring, neurophysiological diagnostic testing including electroencephalograms (EEGs), electromyograms (EMG)s (fine needle), evoked potentials (EPs) both sensory and motor, epilepsy evaluations including synchronized video acquisition and analysis in epilepsy monitoring units, and mobile monitoring while transporting a patient.

In one aspect of the invention, the System provides a modular, intraoperative neurophysiological monitoring system comprising a head module (Computational Module) and one or more serially connected functional modules, each of which contains a communications board (Neuron Board) which contains a USB hub and a field-programmable gate array (FPGA) processor. The serially connected functional modules comprise one or more Data Acquisition modules, an Electrical Stimulation module, and an Auditory/Visual Stimulation module. The serially connected functional modules may be serially connected in any order depending on the preference of the user for a particular procedure. The head module is either a Core computational module which is mounted on a cart, or a portable system utilizing a commercial laptop as the computational module. In either case, the head (or first) module also contains a base board. The base board also contains both a USB hub and an FPGA chip and facilitates data concatenation of all data types being collected.

In another aspect of the invention, the System provides a unique USB hub architecture, which provides power to all modules and allows for bidirectional communications between the modules and for system synchronization. This modified USB architecture provides up to seven cascading tiers of devices including the computational module and the base board comprising the first two devices.

In another aspect of the invention, the System provides a sensing circuit located in each module which senses which module is the seventh or in the last tier in a chain and provides that another module is not connected downstream so that no more than five functional modules are interconnected and that the fifth, or last functional module, is recognized as a device.

In another aspect of the invention, the System provides an electrocautery suppression filter, which is a front-end filter to eliminate high frequency and high voltage noise injected into the system by an electrocautery device. The electrocautery suppression filter allows for continual recording of essential neurological signals during the time that an electrocautery device is being used.

In another aspect of the invention, the System provides common mode noise suppression which utilizes feedback to a patient of the noise component of signals being measured, in which the feedback signal is capable of balancing out common mode noise.

In another aspect of the invention, the System provides DC drift correction by utilizing a reference pin of an instrumentation amplifier which biases the baseline of the output of the amplifier in order to cancel the DC drift from input.

In another aspect of the invention, the System utilizes organic light-emitting diode (OLED) indicators for module number identification and electrode identification by the use of a plurality of full color OLED screens. In an embodiment, there are three full color OLED screens.

In another aspect of the invention, in place of OLED screens, the System utilizes at least one ePaper/eInk display module in the at least three data acquisition modules; at least one ePaper/eInk display module in the at least one electrical stimulation functional module for module number identification and electrode identification; and at least one ePaper/eInk display module in the at least one audio-visual stimulation module for module number identification and stimulus identification. In an embodiment, three ePaper/eInk displays are used in each of the at least three data acquisition modules, two ePaper/eInk displays are used in each of the at least one electrical stimulation module, and two ePaper/eInk displays are used in each of the at least one audio-visual module.

In another aspect of the invention, the System provides A/D conversion which implements signal differencing after digitization in order to generate more data channels than prior art systems, and thus allows for additional ways to present data than previously implemented.

In another aspect of the invention, the System provides a stimulus artifact blanking and trace restore function which allows for data to be acquired without containing contaminating stimulus artifacts and for electrical stimulation to be applied adjacent to recording electrodes, which allows for signals to be recorded through these electrodes immediately after the completion of the stimulating pulses. The application of blanking signals is under the control of a local FPGA chip contained on the communications board.

In another aspect of the invention, the System comprises a plurality of electrical stimulators in the Electrical Stimulation module to produce a variety of train patterns for stimuli which may be synchronized to provide for apparent simultaneous acquisition of multi-modality electrical evoked potentials. The Electrical Stimulation module provides both constant current and constant voltage mode stimulation which can be used interchangeably for electrical stimulation, and which supports both uniphasic and biphasic electrical stimulation, all of which may be interchanged at a user's discretion. The control of these stimulus patterns is provided by the FPGA chip on the communications board. In an embodiment, the Electrical Stimulation module contains eight electrical stimulators.

In another aspect of the invention, the System comprises, in the Auditory/Visual Stimulation module, sound output to ear buds for auditory stimulation and visual output to either a video graphic array (VGA) monitor or to goggles for visual stimulation. Visual stimulation by the VGA monitor is driven through a VGA full color range encoder chip, where patterns are predefined with different color, texture, intensity, and flashing frequency. The full color range stimulation with variety patterns and frequencies makes the system capable of producing complicated visual-related evoked potential signal monitoring. Pattern visual stimulation may also be provided through the goggles. The control of the stimulus patterns is provided by the FPGA chip on the previously described communications board.

In another aspect of the invention, the System comprises a plurality of layers of electrical isolation for a patient in order to isolate the patient from an electrical current path from the patient to earth ground.

BRIEF DESCRIPTION OF DRAWINGS

The patent or application file contains at least one drawing executed in color. Copies of this patent or patent application publication with color drawing(s) will be provided by the Office upon request and payment of the necessary fee.

For the present disclosure to be easily understood and readily practiced, the present disclosure will now be described for purposes of illustration and not limitation in connection with the following figures, where like reference numerals refer to identical or functionally similar elements throughout the separate views.

FIG. 1 shows the NeuroNet-VII system architecture, where the top panel is a NeuroNet-VII system with Computational Module A, containing a core device interface (CDI)-designed core module, and the lower panel is a NeuroNet-VII system with Computational Module B, containing a laptop computer, a CDI adapter module comprising a Base board and power supply, in accordance with an embodiment of the invention.

FIG. 2 is a schematic of the Detailed System Architecture, showing the module interconnection scheme, with red lines indicating power distribution and blue lines information distribution, in accordance with an embodiment of the invention.

FIG. 3 is a schematic of the Base Board (BN7-U003), with red lines indicating power distribution and blue lines information distribution, in accordance with an embodiment of the invention.

FIG. 4 is a schematic of the Neuron Board (BN7-U001), providing universal control and communications, with red lines indicating power distribution and blue lines information distribution, in accordance with an embodiment of the invention.

FIG. 5 is a diagram of the System Synchronization Protocol, in accordance with an embodiment of the invention.

FIG. 6 shows the USB hub structure for the Axon Architecture which allows for 5 functional modules, in accordance with an embodiment of the invention.

FIG. 7 shows the USB hub structure for the Axon Architecture which allows for up to 31 functional modules, in accordance with an embodiment of the invention.

FIG. 8 shows the USB switching circuit design, where (Top Panel) is a downstream module connected and (Bottom Panel) is a downstream module not connected, in accordance with an embodiment of the invention.

FIG. 9 is a schematic showing the Compute Module A, where (Left Panel) shows the Core Board and (Right Panel) shows the Base Board, with red line showing power distribution and green lines showing information distribution, in accordance with an embodiment of the invention.

FIG. 10 is a schematic showing the data acquisition module structure, in accordance with an embodiment of the invention.

FIG. 11 is a schematic of the third order LC active electrosurgical suppression filter, in accordance with an embodiment of the invention.

FIG. 12 are two frequency response curves of the electrosurgery suppression third order LC filter, where (A) demonstrates amplitude response which is flat to 50 kHz, and (B) demonstrates phase response which has 0° phase shift to 3 kHz, in accordance with an embodiment of the invention.

FIG. 13 shows the transient response for the 3-pole active LC filter, in accordance with an embodiment of the invention.

FIG. 14 shows noise analysis of the electrosurgery suppression filter, in which the blue line shows the noise produced by the filter as a function of frequency, in accordance with an embodiment of the invention.

FIG. 15 is a schematic of the circuit design of the common mode noise suppression circuit, in accordance with an embodiment of the invention.

FIG. 16 is a schematic of the DC drift suppression circuit, in accordance with an embodiment of the invention.

FIG. 17 is a schematic showing the differencing operation on the electrode signals to produce the desired data channel, in accordance with an embodiment of the invention.

FIG. 18 is a schematic showing the MOSFET (metal oxide semiconductor field-effect transistor) based artifact blanking and trace restore, in accordance with an embodiment of the invention.

FIG. 19 is a schematic showing the multistage blanking circuit for artifact blanking and trace restoring, in accordance with an embodiment of the invention.

FIG. 20 shows patterns of stimuli provided by the various types of stimulators, in accordance with an embodiment of the invention.

FIG. 21 shows the structure of the electrical stimulator module, in accordance with an embodiment of the invention.

FIG. 22 shows the uniphasic and biphasic stimulus pulses, either current or voltage, in accordance with an embodiment of the invention.

FIG. 23 is a schematic of the conceptual design for the uniphase/biphase pulses, in accordance with an embodiment of the invention.

FIG. 24 shows the structure of the auditory and visual stimulator module, in accordance with an embodiment of the invention.

FIG. 25 is an illustration of the Goggle LED layout and stimulation groups, in accordance with an embodiment of the invention.

FIG. 26 is an assembly drawing showing the system isolation architecture, in accordance with an embodiment of the invention.

DETAILED DESCRIPTION OF THE INVENTION

As used herein, the terms “computational module” and “compute model” are meant to be interchangeable.

As used herein, the terms “head module,” “computational module,” and “first module” are meant to be interchangeable.

As used herein, the terms “communications board” and “neuron board” are meant to be interchangeable.

As used herein, the terms “pod,” “module,” and “component” are meant to be interchangeable.

As used herein, the terms “serially connected functional pods,” “tier,” and “device” are meant to be interchangeable.

Illustrative embodiments of the invention are described below. In the interest of clarity, not all features of an actual implementation are described in this specification. It will of course be appreciated that in the development of any such actual embodiment, numerous implementation-specific decisions must be made to achieve the inventors' specific goals, such as compliance with system-related and business-related constraints, which will vary from one implementation to another. Moreover, it will be appreciated that such a development effort might be complex and time-consuming but would nevertheless be a routine undertaking for those of ordinary skill in the art having the benefit of this disclosure. The systems disclosed herein boast a variety of inventive features and components that warrant patent protection, both individually and in combination.

As shown in FIG. 1, the NeuroNet-VII system comprises two configurations: (1) a cart-based NeuroNet-VII configuration utilizing Compute Module A, which has a Core module as the computational unit, functional modules, and accessories such as display monitor, control tablet, and wireless input devices; and (2) a portable NeuroNet-VII configuration utilizing Compute Module B, which has a commercial PC, a Base Board as an interface between the PC and the downstream series of functional modules. Table 1 shows the difference between these two Compute Modules. Compute Module A (for the NN750/NN770 assemblies) contains a Core Module which include the CDI designed Core board (computational engine), a Base Board which is used as a multi-media data collection board, the CDI designed Speaker module and a medically certified power supply. Compute Module B (for the NN700/NN730 assemblies) consists of a laptop computer, an Adapter module which contains a Base Board and a medically certified power supply, and a Speaker module.

TABLE 1

NeuroNet-VII Compute Module Configurations

Components
Module

Module name
Module types
packaging
components

Compute
Compute
Core module
Core board

Module
Module A

Base board

(NN750/NN770)

Power supply

Speaker

Compute
Laptop
Laptop

Module B
Adapter module
Base board

(NN700/NN730)

Power supply

Speaker module
Speaker

The Compute Module fulfills four functions. (1) It contains a computational engine designed to function as the signal processing, computational center of the system, as well as having features for displaying and storing data. The Compute Module is always the head item in a chain of modules. (2) It provides for data communication to the downstream modules which either acquire data from a patient or provide stimuli to the patient. (3) It provides for the acquisition and integration of data from other devices, which includes, without limitation, anesthesia monitoring devices, imaging systems, and video from microscopes, endoscopes, or other cameras, and the injection of signals into the operating microscope. (4) It provides for connectivity to the internet either through ethernet or wireless connectivity. The Compute Module, in addition to use of a keyboard and display, may be controlled by a tablet connected by BLUETOOTH®. The tablet may also be used to display data.

The System of the present invention is the first intraoperative neurophysiological monitoring (IONM) system designed using modules which are serially connected, or daisy chained, together. The System includes three types of functional modules: (1) Data Acquisition Modules; (2) Electrical Stimulation Module; and (3) Auditory/Visual Stimulation Module. A Data Acquisition Module is designed to acquire data from a subject. The Electrical Stimulation Module and the Auditory/Visual Stimulation Module are designed to stimulate the subject to evoke signals from the subject's nervous system. The modules are designed to be interconnected in any order; i.e., any module may be first in a chain of modules. The System recognizes what the place of each module is in a chain of modules and assigns each module its correct identification. Whichever Data Acquisition Module is the initial acquisition module, has its electrodes assigned numbers 1 through 24 by the system. The second acquisition module's electrodes are assigned numbers 25 through 48 and the third acquisition module has its electrodes assigned the numbers 49 through 72. An acquisition module does not need to be the first module in a chain of modules and the data acquisition modules do not need to be adjacent to each other. As shown in FIG. 1, except for the Compute Module, the two System configurations may be identical.

Table 2 enumerates the electronic boards contained in the Compute Modules and in the Modules.

TABLE 2

Core and Pods Contained in the Electronic Boards

Modules
Boards
Description

Compute Module A
BN7-U003
Base Board

BN7-C001
Core Board, Computer

Processor/Storage

BN7-C002
Power Supply

CN7-C114
Speaker Assemble

Tablet
Alternative method of Display

Control Panel and Data from Core

Data Acquisition POD
BN7-A001
Amplifiers/Filters and A/D

BN7-A002
Electrode Pin/Filer Board

BN7-U001
FPGA/USB Communication Board

BN7-U002
Display Board-Pin Identification

Electrical
BN7-E001
Electrical Stimulation Board

Stimulator POD
BN7-E002
Stimulator Pin Board

BN7-P001
Extender Pod Board

BN7-U001
FPGA/USB Communication Board

BN7-U002
OLED Display Board

Audio/Visual
BN7-B001
A/V Stimulation Board

Stimulator POD
BN7-U001
FPGA/USB Communication Board

BN7-U002
OLED Display Board

(Applied Part)
BN7-G001
Left Eye Stimulation Goggle

(Applied Part)
BN7-G002
Right Eye Stimulation Goggle

BN7-B103
Ear Buds

Compute Module B
Laptop
Standard computer.

Computer

BN7-U003
Base Board (Interface unit

between pods and laptop)

FIG. 2 illustrates the overall module interconnection scheme with red lines indicating power distribution and the blue line indicating information distribution, which shall be described in detail below.

Interconnection Between Modules

The interconnection between the modules is based on a CDI developed architecture, the Axon Architecture which provides power to all the modules, system synchronization between all the modules and which utilizes USB bidirectional communications facilities. Each module is uniquely identifiable as to its type and sequence in the series. Each functional module contains a Neuron Communication board (BN7-U001) which provides the hardware implementation of the functions described in this section. Due to the unique nature of the Axon network architecture, there may be as many as thirty-one modules in a system.

Axon Architecture

The Axon Architecture provides power, system synchronization and communication facilities between all the system modules. There are three hardware components which comprise the Axon Architecture: the Base Board (FIG. 3)/Adapter Module of the Compute Module; the Neuron Board (FIG. 4) in each functional module; and the Axon Cable which interconnects each module.

In order for the Compute Module to be able to control and retrieve data from the functional modules directly with minimum communication complexity, the USB protocol and USB hub architecture is used in the chain of modules as shown in FIGS. 3 and 4. Thus there is one USB hub and one USB adapter on each Neuron Board to provide a USB interface for the current module and the next connected module. With this structure, all the functional modules connected are recognized by the Compute module as USB devices. A proprietary USB communication protocol allows the Compute Module to control and configure the functional modules.

Base Board

The Base Board (FIG. 3) (BN7-U003) is designed to provide three functions: data concatenation, system synchronization of the functional modules with a 32.768 MHz clock and an interface between the Compute Module and the function modules which provides the correct data format looking towards either device. The Base Board is an FPGA based multi-media data acquisition board which can acquire data from multiple sources in the operating room, such as video, images and the anesthesia monitor. To support these functions, it contains HDMI, VGA and Serial Adapter chip sets to support data capture. It has three video connectors: an HDMI input port, a VGA input port, and a VGA output port. The data are encapsulated by the FPGA and sent to the core board through the USB connection. The data from the video and imaging sources and the anesthesia machine are encapsulated and broadcast for viewing.

Neuron Board

The Neuron Board (FIG. 4.) (BN7-U007) provides the interface to the Axon-Cable for the functional modules and supports the USB communications, manages power to the module, and contains a field programmable gate array (FPGA) which controls the function of the module it is in. The Neuron Board provides for module power distribution, module control/data transmission, system synchronization, and controls data retrieved from a specific functional module, such as the data acquisition board of a Data Acquisition module, electrical stimulation board for an Electrical Stimulation module, and visual/auditory stimulation board for visual/auditory stimulation module. A USB 3.0 controller chip is utilized on the Neuron Board to serve as a USB signal adapter between the FPGA chip and the Compute module.

Axon Cable

The Axon-Cable (FIG. 2) provides the interconnection between the modules and provides power as well as all communications between the modules. Table 3 shows the power/signal pins connected in the Axon-Cable. The Axon cable needs to be able to deliver a 5 Amp current at 24 volts. The communication includes two parts: the clock signal for synchronization of all the functional modules and the control/data transmission. The control/data transmission is implemented using the USB protocol. In NeuroNet-VII system, the Compute Module utilizes USB protocol to control/configure the functional modules and retrieve data from them. The system synchronization protocol and the control/data transmission protocol are described below.

TABLE 3

Axon-Cable Power/Signal Connector Specifications

USB Type-C
USB Type-C

Plug #1
Plug #2

Upstream
Downstream

Connector
Connector

Pins
Pins
Signal

A1, A12,
A1, A12,
GND

B1, B12
B1, B12

A4, B4,
A4, B4,
POWER

A9, B9
A9, B9

A2, B2
A2, B2
USB 2.0 D+

A3, B3
A3, B3
USB 2.0 D−

A5, B5
A5, B5
Single ended

reference signal

A6, B6
A6, B6
System synchronization

control +(reserved)

A7, B7
A7, B7
System synchronization

control −(reserved)

A8, B8
A8, B8
Single ended system

trigger signal

A10, B10
A10, B10
System clock CLK+

A10, B10
A10, B10
System clock CLK−

Shell
Shell
Shield

The design utilizes USB type C receptacle as the Axon-Cable connector in the modules. This receptacle meets the power/signal transmission requirements and allows the utilization of a standard receptacle with a unique interconnecting cable. The USB type C plug is also utilized at both ends of the Axon-Cable, which are additionally identified as upstream or downstream connectors. Signal integrity and system stability require that all the signal differential pairs are twisted and individually shielded. The cable also has an outer shield.

System Synchronization Protocol

NeuroNet-VII requires near real time operation in that the acquired data from each data channel is required to be synchronized within 62.5 ?secs for each data sample and stimulus. This ensures that all data are aligned for processing. However, the Compute Module is running a non-real time operating system while the FPGA chips with each functional module, which are responsible for stimulus presentation and data acquisition, have no operating system. To meet this system requirement a synchronization method has been developed which utilizes a system synchronization clock, on the Base Board (FIG. 3) (BN7-U003), which provides a common synchronization signal to each functional module. Therefore the Base board and the functional modules are running under the same clock. The USB control signal (USB 2.0 D+/?), the digital control signals, and the synchronization clock (System clock CLK+/?) are listed in Table 4.

The details of this innovative method are shown in FIG. 5 and are as follows:

- (1) System synchronization request: To start the system synchronization procedure, the user issues an Acquire Data command which requires system synchronization. The Compute Module then sends a USB system synchronization command to the functional modules.
- (2) Functional modules response to synchronization request: When the functional modules receive the system synchronization signal, they send a response back to indicate that the modules are ready for system synchronization. Then the modules detect the digital logic trigger signal for synchronization.
- (3) Digital logic signal for synchronization: After the response message from the function modules is received, the Compute Module sends a digital logic pulse through its general purpose input/output pins to the functional modules. The functional modules are running at higher clock rate and, thus, are able to detect the digital pulse from the Compute Module. Once the trigger pulse is detected, the functional modules reset their internal counters and all the registers to start all modules of the system with the same initial time.

Control/Data Transmission Protocols

NeuroNet-VII utilizes the USB protocol and USB hub structure to support communications between the daisy chained modules. Within this architecture, all the functional modules connected are recognized by the Compute Module as USB devices.

The standard USB hub structure allows up to 7 cascading tiers of devices. The NeuroNet-VII design has this same limitation; however, the NeuroNet-VII design allows branching of devices which may increase the total number of devices to thirty-one.

In the NeuroNet-VII design each tier, except the last (the 7th), is defined by a USB hub, which provides ports for devices in the next higher tier to connect to (FIG. 6). The USB root hub (Tier 1) is directly attached to the USB host controller in the CPU chip of the Core module. The Compute module contains a second hub (Tier 2), which is a device to the Tier 1 hub, and which provides ports for interconnecting to the next module in the chain (Tier 3). Thus, the functional module 1 has a Tier 3 USB hub which connects to a Tier 4 USB adapter located on the same module and a Tier 4 USB hub located on functional module 2. In a fully configured system, the 5th module which is at Tier 7 in the serial chain appears as a device to the Tier 6 USB hub, to meet the USB standard. The portable configuration (laptop based) contains the USB root hub/controller combination in the laptop while the Tier 2 hub is contained in the Base/Brick board (BN7-U003) which provides the interface between the laptop and the downstream modules.

The System design requires the modules to be arbitrarily serially connected in any order, with no requirement as to which module must be last in the chain. Each module has the same Communication board which contains a hub. Thus, to ensure that whichever module is Module 5 (Tier 7) in a chain, the system senses if another module is connected downstream and provides both a guaranty that no more than five modules are serially connected and that there is a switching mechanism to ensure that Module 5 appears as a device.

Modules may be connected into a single system based on the branching architecture as shown in FIG. 7.

Switching Circuit to Implement the USB Hub Architecture

A fully configured NeuroNet-VII system has five modules: three Data Acquisition modules, one Electrical Stimulation module, and one Auditory/Visual stimulation module. As discussed above, the system design requires a switching circuit in each module which can detect if another downstream module is plugged in or if the module is the last module in the serial chain. If a module is determined to be the last module in a serial chain, the USB hub in that module switched out of the circuit making the controller on that hub the last device in the chain. If a particular module is not the last one in the chain of modules, then the switching circuit includes both the hub and the controller as devices for that Tier level. To achieve this, the design has a USB switching circuit within each module to dynamically choose between including the USB hub in the signal path or not. In either case the USB controller is maintained in the signal path since it provides a bidirectional signal path to the FPGA chip.

The switching circuit is triggered by whether the downstream port is loaded or not. Loading is detected by sensing a current on the Ground wire (Pair 5) of the USB connector. If the downstream port is loaded, the USB hub is selected unless the functional module is the 5th in the chain. The USB switching circuit is shown in FIG. 8. In this design, the power load from the Axon Connector is detected. If there is one or more functional modules connected to the system after a particular module, the power and ground pin of the Axon cable would have a load current since the downstream modules get power from the Axon-Cable power and ground wires. The load current is detected and utilized to generate a detection signal. This detection signal is then used to drive the selection signal of the multiplexer circuit on board. The multiplexer circuit shall then switch its connection channel between the USB hub and the USB adapter chip. If a 6th serial module is placed in the chain, the application layer of the software issues a warning to the user that the module will not function and issues a control signal to the switching circuit functionally disconnecting the 6th serial module.

Compute Module

Referring now to FIG. 9, the Core Module is structured as the data processing and central computation unit of the Neuronet-VII system, which uses a Linux based operating system. A laptop serves the same functions for the portable version of the system. The Compute Module consists of two boards: Core Board (BN7-C001) and Base Board (BN7-U003). The Core Board (FIG. 9 Left Panel) is the central control and data processing board. It provides the interface to the modules via a USB type C connector and customized system daisy chained cable. The Core Board receives data from the modules and configures/controls the modules under a USB protocol. The Base Board (FIG. 9. Right Panel) provides a video interface to acquire video data from an operating microscope and endoscope. It also provides a serial port interface to capture data from an anesthesia machine. The video frame data and anesthesia data are transmitted to the Core Board through a USB connector between the Core Board and the Base Board.

Core Board

The Core Board (BN7-C001)(FIG. 9 Right Panel) receives data from the modules and Base Board (BN7-U003). Once the data are received, the Core Board processes, displays, and stores the data. A Linux based operating system runs on the Core Board and manages all computational processes. Neuro, the System's software application layer, is executed on top of the operating system and provides all user interfaces and originates all control signals to the system for operation. The Core Board is an artificial intelligent embedded core enabled computer board. It has an ARM-based CPU, which has two ARM Cortex-A15 cores, one embedded digital signal processing core and an embedded micro-controller core. The Core Board reduces the risk of hardware compatible issues which are a problem with commercial computers. In addition, the Core Board also provides an audio interface for a proprietary designed speaker module with audio power amplifier, an ethernet port, a HDMI video port, and enough USB ports for multiple system accessories. A WiFi/BLUETOOTH® module also is embedded on the Core Board, which makes the Core Board capable of communicating with BLUETOOTH® enabled devices and to connect to an available WiFi network. The wireless module also allows the system to be controlled by a BLUETOOTH® enabled tablet. This configuration allows the system to be controlled remotely and for the data to be easily shown to the surgeon.

Base Board

The Base Board (BN7-U003) (FIG. 9 Right Panel and FIG. 3) is previously described above.

Integration of Operating Room Video Imaging Data Into the Signal Chain

The Base Board contains HDMI and VGA chipsets to support different input formats from possible video sources and imaging equipment. As shown in FIG. 3, there are three video connectors: an HDMI input port, a VGA input port, and a VGA output port. The two input ports are used to capture video from an operating microscope or endoscope. The video frames are collected and integrated into neurological signals into the system, which is used for signal analyzing and patient diagnosis. The VGA output is utilized to export collected signals as video stream which can be integrated with the neurophysiological data and injected into the operating microscope for real time visual feedback.

Integration of Anesthesia Data Into Signal Chain

Anesthesia data is critical for IONM, as anesthesia levels affect the data. The Base Board (FIG. 3) contains a serial port which allows the system to obtain data from an anesthesia machine. The data is collected and integrated together with the other signals for local and remote display as well as for archiving as part of the case record.

Integration with Laptop

The portable Neuronet-VII system utilizes a laptop as the computing unit for data processing, displaying and storage. Since the system is designed as a daisy chained system, not only are there standard USB signals within the interconnecting cable, but also power (Pair 4), ground (Pairs 5 and 6), system clock (Pair 2), and system synchronization signals (Pair 7) in the cable [Table 3]. Therefore, the daisy chained modules, though based on the USB networking standard, cannot be connected directly to the USB type C port of a commercial computer. The Base Board provides an interface between the laptop and the daisy chained modules; i.e., this interface provides a compatible daisy chain port to the downstream modules and compatible classic USB interface to the upstream laptop. As shown in FIG. 3, the Base Board provides a USB type C port to the downstream s modules and a USB type B port to the upstream laptop. The Base Board is recognized by the laptop as a USB device. Thus, the USB hub structure on the Base Board provides the USB connection from the modules to the laptop. The Neuro software application running on the laptop executes the same as on the Core Module.

Data Acquisition Module

The Data Acquisition Module is designed to acquire all types of neurophysiological data which range from 0.1 ?volt to 1000 ?volts in amplitude. As shown in FIG. 10, the structure of the Data Acquisition module comprises: (1) Pin/Filter board (BN7-A002); (2) 24 Channels of amplification with DC drift suppression, feedback noise suppression, and A/D conversion (Bn7-A001); (3) OLED Display board (BN7-U002); and (4) a Neuron board (BN7-U001).

The present invention provides significant innovations which are included in the Data Acquisition module: (1) an electrosurgery suppression filter that eliminates high frequency and high voltage noise from an electrical surgical knife (i.e. Bovie); (2) common noise suppression filter based on feedback to patient; (3) DC drift correction; (4) Signal Blanking with stimulus presentation; (5) OLED channel identification; and (6) Digital differencing.

Electrosurgery Suppression Filter

Electrosurgery is widely used in surgical procedures. However, electrosurgery is problematic because the high frequency (300 kHz-500 kHz)/high voltage (300V-500V) current utilized in these devices is noise from the monitoring perspective which fully saturates prior art systems.

The electrical properties of active components, such as operational amplifier, instrumentation amplifier, and analog-to-digital converters cause active components to be saturated once the input signal is out of range of power input range. Therefore, whenever the surgeon uses an electrosurgery device, the high frequency and high voltage signal saturates the signal pathways, making it impossible to continue recording essential biological/neurological signals from the patient. The signal obtained during the time that an electrosurgery device is being used is noisy, saturated and unsuitable for interpretation.

Even though the signal will return to normal once the electrosurgery device stops operating, it is still important to know what is impacting the nervous system while the device is being used. The present invention provides a front-end filter that eliminates the noise injected by the electrosurgery device, and thus allows the continual recording of essential neurological signals. The front-end filter of the invention is unique and is the first and only such filter incorporated into a system of this type.

Filter Design

The electrosurgery device produces a signal which has a frequency range from 300 kHz to 500 kHz with a 300V-500V signal amplitude. The frequency range of the biological/neurological signals that the invention focuses on are from DC to 3 kHz. An additional constraint is provided by the minimum amplitude of the signals that need to be acquired. The brainstem auditory evoked potentials (BAP) signal is about 0.2 ?V peak-to-peak which defines the amplitude of this minimum signal.

In order to suppress the electrosurgery signal and preserve the signal the user is interested in acquiring, the present invention provides a low pass filter with more than about ?60 dB suppression at 300 kHz and 0 dB at less than about 3 kHz. A resistor based resistor-capacitor (RC) low pass filter is not suitable due to the high thermal noise this design produces compared to the signal requirements. Based on the above considerations, the present invention provides a unique inductor-capacitor (LC)-based third order active electrosurgical suppression filter, shown in FIG. 11, which provides the low thermal noise frequency bandpass properties required for continued signal acquisition without saturation while an electrosurgery device is being used. In addition, the frequency response, transient response and noise analysis of this filter are shown in FIGS. 12-14, in which FIG. 12 shows the frequency response curve (amplitude and phase shift) of the filter; FIG. 13 shows the transient response for the filter, in which the rise time is less than 25 psec; and FIG. 14 shows the noise analysis of the filter.

Feedback Common Mode Noise Suppression

Many devices in the operating room generate common mode noise, such as 60 Hz power line noise and radio frequency noise, which should be canceled with differential input amplifiers. However, in the prior art the front-end circuits contain resistors, capacitors, inductors, and other passive/active electronic components have levels of inaccuracy which provide imbalance in the signal pathways. Thus, common mode noise still remains in the system after the basic differential operation. The present invention provides a unique method utilizing feedback to the patient of the noise component of the signals being measured. This feedback signal balances out the common mode noise due to the input channels not being perfectly balanced and matched.

The following factors were considered in the development of this approach. Circuits with instrumentation amplifiers have high common mode rejection ratios (CMRR). In the present invention, a channel is obtained by differencing a signal electrode with the reference electrode. Therefore, the output of the instrumentation amplifier is considered to be a signal channel. To reduce the common mode noise for each channel, it is necessary to obtain common mode noise from both the positive and negative terminal of the instrumentation amplifier. From the basic three amplifier-based instrumentation amplifier (yellow amplifier) design, it is necessary to use the signal from the middle of the gain resistor (for example R1 and R2 in FIG. 15) to obtain the common mode noise signal. At this point, the common mode noise is collected without compromising the CMRR of the original amplifier.

In the invention, each Data Acquisition Module supports acquiring data from twenty-four electrodes. Therefore, it is necessary to be able to collect common mode noise from all of the 24 electrodes which are in use, and to combine them to feedback onto the patient for noise cancellation.

In many cases, however, not all 24 channels are in use. If these unused channels are kept in the circuit, some common mode noise not directly from the patient would be fed back and thus would itself introduce unnecessary noise onto the patient and thus into the system. Therefore, signals are selected from those channels that are used in a particular case. To accomplish this, a switching array chip is used to dynamically select channels into the common mode noise sensing loop based on which channels are activated in the Neuro software application. FIG. 15 shows the design of the common mode noise suppression circuit. In this design the sensing point uses R3 (and R6 through R12) to provide feedback to an operational amplifier which allows the noise from all 24 electrodes to be switched in and combined appropriately.

DC Drift Correction

The DC value or the baseline about which a signal drifts changes over time. This effect is called DC drift. The rate of this drift is influenced by several factors, the most significant of which is electrode polarization. This occurs at each electrode, in different quantities and at different rates, and this discrepancy in charge accumulation creates a voltage that is measured by the system (a.k.a. a battery effect). Thus, the System measures this additional voltage in series with the physiological signal.

As the polarization continues, this voltage continues to build up and the baseline value of the physiological signal changes with it. The baseline would eventually drift beyond the range of the amplifier and only a flat line would be seen in data from the amplifiers. The rate of change in the baseline voltage is on the order of that of slow cortical potentials, and thus this “battery effect” voltage can obscure very low frequency signals of interest.

There are several methods available to remove this DC drift. One common way is to introduce a blocking capacitor at the input of an operational amplifier in the acquisition system. This, however, has the undesired effect of removing low signal components as well as the drift potential.

The present invention provides an alternative design circuit, shown in FIG. 16, which accomplishes several other considerations besides eliminating DC drift. These are: (1) to retain the very low frequency components; (2) to minimize the input thermal noise, which is white noise to the system and almost impossible to filter out; (3) to ensure that the common mode noise canceling circuit is not affected by the feedback loop introduced for the drift canceling circuit. The design circuit utilizes the reference pin of the instrumentation amplifier, which is used to bias the baseline of the amplifier output to cancel the DC drift from the input. One integrator circuit is introduced to accomplish the DC drifting integration and feedback.

OLED Indicators for Electrode Identification

In one embodiment of the present invention, there are three full color OLED display screens utilized in each Data Acquisition Module to display the module number and electrode identification. The same OLED screens are utilized in the Electrical Stimulator Module and the Audio/Visual Module to identify the module number and electrode identification.

ePaper/eInk Display for Electrode Identification and Module Number Identification

In another embodiment of the present invention, in place of utilizing OLED display screens, the System utilizes three ePaper/eInk display modules in each of the at least three data acquisition modules, two ePaper/eInk display modules in the at least one electrical stimulation module, and two ePaper/eInk displays modules in the at least one audio-visual stimulation module.

The ePaper/eInk displays have several advantages over the use of OLEDs with respect to noise, power, heat, display resolution, lifetime, degradation, number of colors, and controllability. Specifically, ePaper/eInk displays are energy efficient due to their ability to reflect ambient light and the need to use power only when a displayed image changes, compared to OLEDs which use backlighting to display images and require constant power input. This energy efficiency reduces heat production and also reduces noise that typically is produced by OLEDs, which enhances the quality of the signals being collected. Second, ePaper/eInk displays have higher resolution and contrast ratio than OLEDs due to their ability to reflect light in a similar manner as paper, and thus are easier to read in various lighting conditions such as bright sunlight and dim lighting. Third, ePaper/eInk displays have a longer lifetime compared to OLEDs, as the backlighting display of OLEDs degrade with time and use. In the System, a static image is displayed on a screen for an extended period of time and when OLEDs displays are used, some pixels are overused and degrade faster creating discoloration on the OLED screen. Such pixel degradation does not occur with the ePaper/eInk displays. Fourth, ePaper/eInk displays provide four colors (black, white, red and yellow) compared to three colors provided by OLEDs. Finally, ePaper/eInk displays support regional updating in a minimum amount of time, which allows for easy implementation of emergency signaling functionality.

Signal Differencing After Digitization

In all the prior art systems, the difference between the electrode signals is performed on the analog signals prior to digitization. This provides a remarkable limitation on the flexibility of how data channels are constructed. In this System, the electrode signals are digitized and then differenced. This provides complete flexibility as to how data channels are defined. The ith Channel is defined to be the difference between two digitized de-referenced electrode signals:

$Chn i^{*} = {ChnNSMR}^{*} = {DsigNS}^{*} - DsigMR * 1$

where digitized de-referenced electrode signal, DsigNS* or DsigMR*, is the digitization of the de-referenced electrode signal, drsigNS or drsigMR. The digitization is implemented by an analog-to-digital convertor. The de-referenced electrode signal is the difference between the electrode signal and reference signal for each electrode signal:

${drsigNS}^{*} = {esigNS}^{*} ? {refsig}^{*}$

where esigNS is the buffered signal from the Sth active electrode in the Nth electrode module, and refsig is the buffered signal for the patient iso-ground.

With this method, which crosses the boundary between hardware and software, shown in FIG. 17, one can generate more channels by differencing different pairs from arbitrary electrodes of any of the Data Acquisition modules, which gives more possible ways to present data.

Stimulus Artifact Blanking Trace Restore Function

There are situations in which the input signals need to be blanked (i.e. held to ground) to prevent the amplifiers from saturating, for example when electrical stimulation is applied, most importantly with transcranial electrical stimulation to obtain motor potentials. In these situations, a stimulus artifact can be observed through the active signal paths. To eliminate the effect of these artifacts, the System provides a logic triggered signal path to pull the input terminals of different amplifier stages to analog ground in real time. This both protects the input terminals and prevents the stimulus currents from leaking into the recorded signal data stream.

A second function which is accomplished by the same circuit is Trace Restore. The DC Drift Correction circuit filters out very low frequency signal, and thus the circuit has a long time constant, which requires a longer time for the signal to settle which interferes with the early signal features. Therefore, the Trace Restore circuit provides a way to settle the signal as fast as possible. The method that is used is the same as stimulus artifact blanking described above. The circuit design is shown in FIG. 18. In this circuit, an N-channel MOSFET is utilized as a controllable switch to provide a path for the signal to the analog ground. A high (logic 1) control closes the MOSFET switch, and the input terminal of the amplifier is pulled to analog ground. In normal operation (logic 0), the input terminal is the input path for the signal. Because the signal path is on all the time, this function is applied to multiple stages of the input analog circuit. FIG. 19 shows the multiple stage implementation of the inventive design for artifact blanking and trace restoring.

Stimulus Patterns

As shown in FIG. 20, stimulators can produce a variety of train patterns for stimuli. These patterns have different situations in which they may be useful. Prior art systems produce most of these patterns except for Random interstimulus intervals.

Electrical Stimulator Module

As shown in FIG. 21, the Electrical Stimulator module contains four boards: a pin board (NN7-E002), a function board (NN7-E001), an FPGA communication board (NN7-U001), and an OLED board (NN7-U002). There also is an extension module (NN7-E003) which may be plugged into the stimulator module.

Constant Current Constant Voltage

Products on the market support only either constant current or constant voltage mode for electrical stimulation. The Neuronet-VII system of the present invention provides both constant current and constant voltage modes, which may be used interchangeably for stimulation. The stimulation ranges are as follows:

Constant Current

The stimulator provides three ranges of selectable stimulating currents. i) 0.1 to 20 mamps (for brain, brainstem and cranial nerve stimulation); ii) 1.0 to 100 mamps (for peripheral nerve stimulation); and iii) 1.0 to 200 mamps (for transcranial stimulation).

The constant current outputs for all three ranges have a linearity of 1%. This also is defined as the relative accuracy of the stimulators.

The constant current stimulation provides for controllable intensity levels as defined here: (i) for 0.1 to 10 mamps, 100 steps with a precision of 0.1 mamps; (ii) for 1.0 to 100 mamps, 100 steps with a precision of 1 mamps; and (iii) for 1.0 to 200 mamps, 100 steps with a precision of 2 mamps. The stimulator provides three ranges of selectable stimulating voltages: (i) 0.1 to 20 volts (for brain, brainstem and cranial nerve stimulation); (ii) 1.0 to 100 volts (for peripheral nerve stimulation); and (iii) 100 to 200 volts (for transcranial stimulation).

The constant voltage outputs for all three ranges have a linearity of 1%. This also is defined as the relative accuracy of the stimulators.

All three constant voltage stimulus levels provide for controllable intensity levels as defined here: (i) for 0.1 to 20 volts, the required step precision is 0.1 volt; (ii) for 1 to 100 volts, the required step precision is 1 volt; and (iii) for 100 to 200 volts, the required step precision is 1 volt.

Uniphasic/Biphasic Stimulation

The NeuroNet-VII System is the only system which supports both uniphasic and biphasic stimulation for electrical stimulation, shown in FIG. 22. The inventive circuit design uses a fast switching array chipset which provides very short delay phase switching of less than 5 ?sec for biphasic stimulation. The conceptual design of using switching array to implement uniphasic/biphasic stimulation is shown in FIG. 23.

Auditory Visual Stimulator

The Auditory/Visual Stimulator module supports output to ear buds for auditory stimulation, and output to either a VGA monitor or goggles for visual stimulation. The structure of the Auditory/Visual Stimulator module is shown in FIG. 24.

Full Color Complex Pattern Visual Stimulation With VGA Monitor

One method of providing visual stimulation is by a monitor driven through by a VGA full color range encoder chip. Patterns are predefined with different color, texture, intensity, and flashing frequency in the System user interface. This information then is sent through the USB communication network to the FPGA, where it is parsed and transferred to the encoder chip for display. The full color range stimulation with variety patterns and frequency makes the System of the present invention more capable for the complicated visual-related evoked potential signal monitoring than prior art systems.

Goggle With Various Block Patterns

In prior art IONM systems, a stimulation goggle has a stimulation pattern which is a full flashing screen. The inventive System design implements stimulation patterns by grouping LEDs into a 3 by 4 matrix in each eye with each block having 2×2 LEDs, as shown in FIG. 25. This design allows the goggles to support various stimulation patterns provided to a patient during surgery.

System Isolation Architecture

The NeuroNet VII system of the present invention has to be well isolated in order to isolate a patient from a current path from the patient to earth ground. Because this system includes both analog and digital electronic circuitry, the isolation barrier implemented in the System contains both analog and digital isolation. The first layer of isolation is power isolation obtained by utilizing a medical grade AC/DC power regulator. This power regulator enables medical grade current leakage from our system to the earth ground. The second layer of the isolation barrier consists of two parts: the first part is an isolated DC/DC power regulator which isolates the digital power supply from the analog power domain; and the second part is the control signal isolation chip which makes it possible for the analog circuits to be controlled by the digital control unit without providing a current path from the subject to the earth ground. FIG. 26 shows the System Isolation Architecture. This is the equivalent of having three layers of electrical isolation.

While the invention has been particularly shown and described with reference to embodiments described above, it will be understood by those skilled in the art that various alterations in form and detail may be made therein without departing from the spirit and scope of the invention, as defined by the appended claims.

	Number	Date	Country
Parent	17901376	Sep 2022	US
Child	18787064		US

Modular Neuronet-VII Intraoperative Neurophysiological Monitoring System

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