Patent Description:
Currently, when measuring pressure within a needle or catheter, there is no ability to identify false-positives of a cardiac pulsewave detected in the needle or catheter as opposed to pressure changes which truly represent the cardiac pulsewave. As used herein cardiac pulsewave is defined to mean a pressure waveform which contains a signal which originates from the contraction of the heart or vessels, and therefore contains information representing, the cardiac pulse. It is conceivable that a needle or an indwelling catheter can detect a non-cardiac pulsation from a variety of non-cardiac sources within the body, including respiratory changes, muscle movements of the diaphragm, etc, and can falsely report that detected pulsation as the cardiac pulsewave. It is also conceivable that patient bodily movements, such as postural changes in position of the patient, could produce pressure changes that are measured and are misinterpreted as originating from the cardiovascular system. In particular, existing devices do not include an independent means to verify that a particular pressure waveform is from the heart, and thus cannot rule out false positives in which the detected waveform has come from a source other than the cardiovascular system. At the same time, determining the location or the patency of a needle or catheter is of great interest to the clinician, such as for delivering of a drug to a patient. Hence, the ability to ensure that the pressure being sensed is not confused with other pressure changing waves produced in the body is of great interest if one is to rely on this information as indicative of needle or catheter placement, which, in turn, will impact patient outcome.

For example, in clinical use, after the placement of a needle or catheter it is common to deliver a dose of medication. Subsequent administrations through a needle or catheter can be compromised due to potential blockage of the needle or catheter, or by migration of a needle or catheter from the original position. Therefore, catheter assessments may be required including determining if a catheter is clogged, determining if the catheter is fully functional, and determining if the catheter has moved from the initial location. The inability to accurately differentiate a catheter's function leaves the clinician in a serious and sometime dangerous quandary: is the failure due to effectiveness of the drug, movement of the catheter, a clogged catheter from precipitate or a blood clot?.

The data also show that between <NUM> to <NUM>% of all catheters need to be replaced on patients because of catheter migration after placement. Clinicians have difficulty determining the reason for the failure of a catheter. Typically it takes to <NUM> to <NUM> minutes to evaluate catheter function and placement as the clinician waits for an observation to a therapeutic drug response, because currently this is the only means to evaluate catheter function. This adds additional risks and additional costs to healthcare systems, as a non-functional catheter can require life-threatening time to assess. Thus, the difficulties and potential risks of catheter placement and monitoring are serious challenges, and therefore a predictable manner to differentiate these conditions would be of great value to patients and clinicians.

Even so, existing devices developed to detect pulsatile waveforms can be expensive and complicated to use, requiring the use of an electro-mechanical motor to deliver the fluid to the patient. Such devices do not allow a clinician to observe an objective pressure generated while manually infusing a drug using a handheld syringe as is typically or preferably done. Existing systems are also not designed with inputs from multiple sources to separately compare and analyze both a heart-beat and pulsatile pressure waveform during use, and so do not provide two distinct physiologic sources of heart rate to determine and verify needle or catheter location. As such, the inventors, in arriving at the present invention, have recognized deficiencies in prior art devices and methods for needle or catheter placement, such as the ability to: <NUM>) detect an input source of a cardiovascular system in which the heart-rate is used for direct comparison with needle or catheter location; <NUM>) detect a cardiovascular response via a direct fluid path and analyze the information in the fluid path to produce beats-per-minute analyses to compare to a secondary source which is known to be detecting a heartbeat; <NUM>) correlate and analyze more than one signal to determine that a needle or catheter is properly placed within an anatomic location; and <NUM>) to provide a positive alert when these two signals are correlated within a range to confirm a true-positive. <CIT>) relates to systems and methods for epicardial electrophysiology and other procedures are provided in which the location of an access needle may be inferred according to the detection of different pressure frequencies in separate organs, or different locations, in the body of a subject. Methods may include inserting a needle including a first sensor into a body of a subject, and receiving pressure frequency information from the first sensor. A second sensor may be used to provide cardiac waveform information of the subject. A current location of the needle may be distinguished from another location based on an algorithm including the pressure frequency information and the cardiac waveform information.

Nevertheless, there is a need in the art for inexpensive and simple devices and methods that are capable of eliminating false-positives when locating a needle or catheter in the body which devices and methods would be of great value to the clinician and to the treatment of patients.

The present invention is defined as set out in the appended claims.

In view of the above-noted and other needs, the present disclosure provides devices and methods which use two or more different physiologic sources indicative of the cardiac pulse to determine needle or catheter placement prior to medication delivery or fluid aspiration. One of the sources may be the cardiac pulsewave detected as a pressure waveform in the needle or catheter, such as by an in-line pressure sensor, and a second source may be heartbeat detection from a finger pulse sensor, for example, or other location known to emit the cardiac pulsewave or heartbeat. The two physiologic sources may then be compared to verify that the pressure waveform detected in the needle or catheter is in fact the cardiac pulsewave, thus eliminating false-positive indications of the cardiac pulsewave in the needle or catheter. The comparison may be performed as a correlation analysis of signals from the two different physiologic sources to determine if the frequency of the signals from the two different physiologic sources is clinically comparable. The correlation analysis may be performed as a comparison of the numerical value of heart rate in beats-per-minute as detected at each of the two or more different physiological sources and/or by cross-correlation of waveforms detected at each of the two or more different physiological sources, for example. Thus, the present invention can perform "Needle/Catheter Location Correlation Analysis" as a comparison of two or more cardiovascular signals which may include beats-per-minute, cross-correlation of pressure waveforms, and/or objective pressure measurements, for example, to determine the location of a needle or a catheter within a mammalian body.

Positive verification of the cardiac pulsewave in the needle or catheter may establish both the correct position of the needle or catheter and its patency. As a result, devices and methods of the present invention can allow clinicians to more easily assess in real-time proper needle or catheter placement with confidence, due to the verified detection of the cardiac pulsewave. These may be presented to the clinician as a signal or an alert confirming proper needle or catheter placement. As a result, with the verified real-time detection of the cardiac pulsewave in the needle or catheter the clinician may use a manual syringe rather than an automated mechanical pump such that the clinician can personally position the needle and control the delivery of medication or aspiration of fluid and the accompanying physical force applied to the syringe. More precise control of the physical force by the clinician can also prevent catheter movement from excessive pressures. Excessive pressure during medication delivery could cause the dislodgement of the needle or catheter from a site as uncontrolled fluid pressures produce a "jet-stream" at the tip of the catheter or needle.

Devices disclosed herein may provide a clinician with an objective (i.e. measured) pressure value in the needle or catheter during the flushing stage. Knowing the objective pressure as a medication is injected can also assist the clinician in avoiding excessive force, preventing excessive pressures. For example, the present invention may alert the clinician when a pressure value has been exceeded. The alert can be audible, visual, haptic or the like.

Exemplary uses of devices and methods of the present invention may include locating a needle within the body to a specific target site, such as that of an epidural procedure or peripheral nerve block. In particular the identification of the epidural space, the determination of needle proximity to a neurovascular bundle in regional peripheral nerve blocks, and other medical procedures which require a needle or catheter tip to be positioned at a specific location (e.g., intrathecal, intravenous, intra-arterial, organ of the body) where the cardiac pulse is present, all can benefit from devices and methods of the present invention. Accordingly, the use of devices and methods of the present invention at such exemplary target sites can with greater reliability replace the current Loss-of-Resistance technique (LOR-technique). Further to its advantages, devices and methods of the present invention may be used for all types of needles and catheters that are placed into patients at anatomic sites at locations that emit a rhythmic pulsation of the arterial system, and may be provided as an inexpensive and portable system.

The apparatus disclosed herein may achieve a number of objectives. For example, an objective of the invention may be to detect a pulsatile waveform of a catheter which is verified for the presence of a cardiovascular pulse by comparing a first input to a second input from the cardiovascular system, such as a heartbeat detected from a second input source. The redundant nature of these two sources may be identified and confirmed electronically and produce an alert to the operator. A further objective of the present invention may be to provide an inexpensive device to determine an objective pressure value that is generated when a drug is injected through a catheter using a manual syringe to prevent excessive pressure production at the tip of a catheter that might dislodge the catheter from a target position. Devices of the present invention can enable an audible alert to be set for a maximum pressure value to alert the operator if they have exceeded a specific pressure value. In addition, a further objective may be to detect and display a pulsatile pressure waveform corresponding to the pulse of the cardiac-vascular system to determine the position of a catheter. A further objective of the invention may be to provide a method and device that can detect the pulsatile pressure waveform that is present in the epidural space or intrathecal space of the central nervous system and detecting a pulsatile waveform or the proximity to the neurovascular bundle of nerve. A further objective may be to observe an objective pressure and graph an objective pressure value over time to monitor the response to an injection performed with a manual syringe to determine the patency of a catheter. Another objective may be to correlate an objective pressure value with a pulsatile pressure waveform to determine the patency and position of a catheter by simultaneously viewing the pressure/time graph and the pulsatile pressure waveform to determine catheter function. A further objective may be to provide a mean value of a pulsatile pressure waveform from an intravenous catheter to determine the patency of said catheter before, after and during an infusion.

In particular, in a first exemplary configuration, the present invention may provide an apparatus for confirming placement of a hollow-bore structure at a desired treatment location in a mammalian subject. The apparatus may include a first sensor operably connected to a lumen disposed in the hollow-bore structure; the first sensor may be configured to provide a first signal in response to detection of a first property indicative of a cardiac pulse in the lumen of the hollow-bore structure. The apparatus may include a second sensor configured to provide a second signal in response to detection of a second property indicative of the cardiac pulse. A controller may be operably connected (wirelessly or wired) to the first and second sensors to receive the first and second signals, and maybe configured to compare the first and second signals to provide a comparison result, whereby the comparison result provides an indication of placement of the hollow-bore structure relative to the desired treatment location. The first and/or second physical property may be one or more of a pressure, change in fluid volume, an electrical signal, and an optical signal. The first and second properties may relate to the same physical property or different physical properties indicative of the cardiac pulse. The hollow-bore structure may include one or more of a needle and a catheter. The first sensor may include an in-line pressure sensor having a sensor lumen disposed in fluid communication with the lumen of the hollow-bore structure, and the second sensor may be a finger pulse sensor. One or more of the first and second sensors may include a memory configured to store an indication that the first or second sensor, respectively, has been used. The device may also include an identification circuit embedded within or connected to one or more of the first and second sensors, wherein the identification circuit is configured to provide a signal to the controller, the signal including one or more of: a configuration signal indicative of physical characteristics of the first or second sensor; a verification signal indicative of the first or second sensor; and a use signal so that the controller can detect the number of times or length of time the first or second sensor was previously used.

A second exemplary configuration disclosed herein is an apparatus for confirming placement of a hollow-bore structure at a desired treatment location in a mammalian subject having a controller configured to receive a first signal from a first detector placed at the treatment location. The first signal may be indicative of a cardiac pulse in the hollow-bore structure. The controller may also be configured to receive a second signal indicative of the cardiac pulse from a second detector placed at a second location. The controller may be programmed to compare the first and second signals to provide a comparison result, whereby the comparison result provides an indication of the placement of the hollow-bore structure relative to the desired treatment location.

For both the first and second (or other) exemplary configurations, the first and/or second signal may represent one or more of a pressure, change in fluid volume, an electrical signal, and an optical signal. The first signal may have a first period and the second signal may have a second period, and the controller may be configured to compare the first and second periods to provide the comparison result. (In addition, the first signal may include a waveform having a first period and the second signal may include a waveform having a second period, and the controller may be configured to compare the first and second periods to provide the comparison result. ) Further, the first signal may include a first numeric value indicative of a frequency of the first signal, and the second signal may include a second numeric value indicative of a frequency of the second signal, and the controller may be configured to compare the first and second numeric values. One or more of the first and second numeric values may be a cardiac pulse in beats-per-minute. The controller may also be programmed to perform a cross-correlation analysis of the first and second signals. The controller may be configured to create an alert signal when the comparison result is within a selected value. In addition, a display may be operably connected to the controller for receiving one or more of the first and second signals and the comparison result from the controller. In one desirable configuration, the controller may include the display. The display may include a first data section for displaying a pressure detected by the first sensor in the lumen disposed in the hollow-bore structure, and may include a second data section for displaying the first and second signals. The first and second signals may each include a respective waveform, and the second data section may include a graph displaying the respective waveforms of the first and second signals. The display may also include a section for displaying an alert indication when the comparison result is within a selected value. The alert may be one or more of an auditory, visual, and haptic signal.

The foregoing summary and the following detailed description of exemplary embodiments of the present invention may be further understood when read in conjunction with the appended drawings, in which:.

Referring now to the figures, wherein like elements are numbered alike throughout, <FIG>, <FIG> schematically illustrate exemplary configurations of devices <NUM>, <NUM> of the present invention for determining proper placement of a hollow-bore structure, such as a needle <NUM> and/or catheter <NUM>, at a selected treatment location in a patient <NUM> using at least two independent measurements of the cardiac pulse, one of which measurements is detected via the hollow-bore structure. For example, the detection of the cardiac pulse via the needle <NUM> and/or catheter <NUM> may be accomplished by sensing a physical property in the lumen of the needle <NUM> and/or catheter <NUM>, such as a physical property representing the pressure or fluid volume change in the lumen, where the variation in the pressure or fluid volume change contains a signal created by, and indicative of, the cardiac rhythmic contraction, e.g. the cardiac pulsewave. In particular, an in-line pressure sensor <NUM> may be provided in fluid communication with, and between, the needle <NUM> (or catheter <NUM>) and a manual, handheld syringe <NUM>, <FIG>, <FIG>.

The second of the two independent measurements may be detected by a second device, such as a finger pulse sensor <NUM>, disposed at a location on the patient <NUM> at which a physical property representing the cardiac pulse may be detected, <FIG>. The physical property may be a pressure, an electrical signal, an optical signal, or other suitable signal, for example, that provides for independent verification of the presence of the cardiac pulse detected in the needle <NUM> and/or catheter <NUM>. The physiologic location of the second device <NUM> may be different from that of the needle <NUM> and/or catheter <NUM>.

Through the use of two independent measurement sources <NUM>, <NUM> for the cardiac pulse, devices <NUM>, <NUM> of the present invention can compare the signals from the two separate sources <NUM>, <NUM> to confirm that the signal from the needle <NUM> and/or catheter <NUM> is indeed the cardiac pulse, which in turn will confirm that the needle <NUM> and/or catheter <NUM> is in the "correct" location for procedures in which the target tissue is one in which the cardiac pulse is expected to be present. For example, target sites for correct needle or catheter placement in which the cardiac pulse is expected to be present include the epidural space, intrathecal space, or proximate to a neurovascular bundle or other anatomic structure that emits a pulsatile wave produced by the cardiovascular system, including the heart itself.

Once confirmation of needle or catheter placement is confirmed by the device <NUM>, <NUM>, an alert may be provided to the clinician, and the clinician may proceed with injection or aspiration through the syringe <NUM>, depending on the nature of the procedure being performed. The alert may be provided in any suitable form, such as auditory, visual, or haptic, for example. Thus, devices of the present invention are capable of location guidance and confirmation during the placement of a needle <NUM> and/or catheter <NUM>. Indeed, devices and methods of the present invention may confirm patency of the needle <NUM> and/or catheter <NUM>.

Turning to <FIG> in more detail, operation of the sensors <NUM>, <NUM> may be provided by a dedicated controller device <NUM>. The controller device <NUM> may be operably connected to the sensors <NUM>, <NUM> via respective cables <NUM>, <NUM>, and in certain cases an adapter <NUM> may be provided between the controller device <NUM> and a respective cable <NUM>. Alternatively, the sensors <NUM>, <NUM> may communicate wirelessly with the controller device <NUM>, via any suitable communications technology such as Bluetooth® communication. The sensor <NUM> disposed in sensing communication with the needle <NUM> and/or catheter <NUM> may, as described above, be an in-line pressure sensor whose fluid path is continuous with the needle <NUM> and/or catheter <NUM>, such as a Merit Medical, MER200. In such a case, the contraction of the heart produces propagation of an energy wave representative of the cardiac pulse into a fluid in the sensor <NUM> and the wave may be measured through pressure or volumetric changes therein. The changes may produce a repetitive signal in the form of a pulsewave signal and may be measured from peak-to-peak or zero crossings to determine the frequency of the pulsewave signal to yield the cardiac pulse rate in beats-per-minute. Alternatively, the sensor <NUM> could be positioned alongside the catheter <NUM> and/or could be interposed between an external fluid source such as an IV bag, syringe or any vessel that provides a continuous fluid line.

In addition, the sensor <NUM> (and/or sensor <NUM>) may be one or more of an acoustic sensor, optical sensor, infrared detector or other device which detects the cardiac pulse which has propagated within tissues from the cardiovascular system to the location of the sensor <NUM>, <NUM>. In short, any sensor type capable of detecting the cardiac pulse in the lumen of the needle <NUM> and/or catheter <NUM>, whether by pressure, sound, or other physical property, may be used as the sensor <NUM>. Similarly, any sensor type capable of detecting the cardiac pulse at a physiologic source independent of the lumen of the needle <NUM> and/or catheter <NUM> may be used as the sensor <NUM> including one based on photophelthysmography (PPG) such as a Model <NUM> USB or Model <NUM> Bluetooth® Low Energy from Nonin® Medical, Inc, for example. Alternatively, the sensor <NUM> may be provided as a pneumatic inflatable cuff (such as that found in a sphygmomanometer). With a preference for using non-invasive methods for detecting the heart beat or beats-per-minute of the peripheral vascular system, it is also possible that the detection of the heart beat could be from an electronic signal that is captured with a heart-rate monitor in contact with the skin of a patient.

One or more of the sensors <NUM>, <NUM> may also be provided in the form of a single use sensor which may be particularly desirable in the case where the sensors <NUM>, <NUM> come in direct contact with bodily tissues or fluids, e.g. blood, cerebrospinal fluid, or fluid filled epidural space. For example, the sensor <NUM> may include a separate body fluid pressure sensor <NUM> and a microchip in the form of a programmable memory <NUM>, <FIG>, where the programmable memory <NUM> may be used to track usage of the sensor <NUM> and thereby limit the sensor <NUM> to a single use. Information communicated with the sensor <NUM> and memory <NUM> may be encrypted and coded to ensure security of the use of the sensor <NUM>. Alternatively or additionally, sensor <NUM> can have an internal on-chip timer that allows a specified amount of time for use of the sensor, after which the sensor <NUM> expires. These features mitigate the potential for use on multiple patients and help to control against counterfeit products. The sensor <NUM> may be similarly configured for single use.

The data collected from the sensors <NUM>, <NUM> may be transmitted to the controller device <NUM> for further processing, after which the processed data may be transmitted via a cable <NUM> or wirelessly to a display device <NUM>, such as a computer, smart phone, tablet, or other handheld device, for viewing by the clinician, <FIG>. The controller device <NUM> may include a circuit board, central processor unit, rechargeable battery, connectors for wired communication, and/or antennas for wireless communication via Wi-Fi, Bluetooth® or other suitable communications standard. The controller device <NUM> may both process the received data and control and provide power to the sensors <NUM>, <NUM>. The display device <NUM> may also further process the data prior to display and may include a variety of input elements such as buttons, a touchscreen, voice activated commands, scanning, etc. to transfer information into the controller device <NUM>. Alternatively, the display device <NUM> may receive the data directly from the sensors <NUM>, <NUM> and control the operation of the sensors <NUM>, <NUM> so that a separate controller device <NUM> is not required, <FIG>. In this regard, the display device <NUM> may include a software application that can collect, process and display input data received from the two or more separate input sources <NUM>, <NUM> with or without use of the controller device <NUM>. The data to be displayed by the display device <NUM> may include, but is not limited to, an objective pressure value <NUM>, a graph of objective pressure over time <NUM>, and a pulsatile waveform <NUM> representative of the contractive nature of the heart or cardiovascular system, <FIG>. A prototype of the device controller <NUM> was constructed for use in the system <NUM> of <FIG>.

<FIG> illustrates a schematic of the circuit <NUM> used in the prototype controller <NUM> of <FIG>. (The circuit <NUM> also represents at the component-level implementation of block diagram elements shown in <FIG>. Reference to corresponding elements of <FIG> are provided parenthetically. ) As shown in <FIG>, two different communication options were provided, and both were tested: wireless communications via Bluetooth® transceiver U2 (e.g., transceivers <NUM>, <NUM>, <FIG>), and direct wire communications via the USB serial data cables <NUM>, <NUM>, <FIG>, connected to connector J1, <FIG>. (Specifications for all components of the circuit <NUM> are provided in Table <NUM> below. ) The prototype <NUM> collected data from the two sensors <NUM>, <NUM> and provided the data to the controller <NUM> where the data were formatted for presentation to a user.

In the prototype <NUM>, a Nonin Medical, Inc Xpod® 3012LP External OEM Pulse Oximeter with 8000A Reusable Finger Clip pulse oximetry sensor was used for the finger pulse sensor <NUM>. The finger pulse sensor <NUM> produced a continuous stream of serial data which were input on connector <NUM>. The data from the finger pulse sensor <NUM> were provided to the unit serial input receiver channel <NUM> at pin <NUM> of a microprocessor U3 (e.g., microprocessor <NUM>, <FIG>). A standard baud rate transmission was used which was set by resistor R16. The data were collected and assembled into a format simplified for use by the display device <NUM>.

The in-line pressure sensor <NUM> was a piezoresistive bridge design Model MER200 from Merit Medical, Inc and was attached to connector J4, <FIG>. The reference voltage used to power the in-line pressure sensor <NUM> was provided directly from the lithium-ion battery BT1 in the circuit <NUM>. The in-line pressure sensor <NUM> was connected through an adapter <NUM>, <FIG>. The adapter <NUM> had several functions: to easily connect the sensor <NUM> to the controller <NUM> through an RJ12 quick connection connector J12; to provide power turn-on by interlock connection to the battery BT1; and, to permit identification and use management of the in-line pressure sensor <NUM> by a one-wire memory device.

A memory device <NUM> may be present in the in-line pressure sensor <NUM>, <FIG>, to identify and serialize the in-line pressure sensor <NUM> allowing traceable data to be collected and stored by the display device <NUM>. In the prototype such a memory device was in the adapter <NUM>. Use of the memory device <NUM> could also help mitigate the potential for use of the pressure sensor <NUM> on multiple patients. The sensor <NUM> and adapter <NUM>, <FIG>, may be disposable components intended for single use on one patient.

Since the device <NUM> had a user accessible connector J4, the circuit <NUM> included a protection against Electro-Static Discharge (ESD) events which could be caused by the accumulation of excessive static charge. Diodes D4-D9 were used to clamp the inputs of connector J4 to protect the internal circuitry, <FIG>. The adapter <NUM> internally jumpered together pins <NUM> to <NUM> at connector J4, <FIG>, which provided a connection path from the internal battery BT1 negative terminal to the remainder of the components of circuit <NUM>. Thus, the circuit <NUM> was powered on when the adapter <NUM> was attached to the connector J4, which also helped mitigate exposure leakage current to users and patient when no adapter was present. Connector J4 was also used to charge the battery BT1 using an external charger <NUM> attached to J4 via cable <NUM>, <FIG>. The circuit <NUM> was not powered when the charger <NUM> was attached; only the battery BT1 was charged. The charge current was limited and monitored to provide protection against battery fault/fire protection.

As shown in <FIG>, the signal from the in-line pressure sensor <NUM> was presented to chip U4, a high resolution <NUM>-Bit analog-to-digital converter, (e.g., A/D converter <NUM>, <FIG>). The analog-to-digital converter U4 used, for its reference voltages, the same battery/ground voltage that powered the in-line pressure sensor <NUM>. Hence, the analog-to-digital converter U4 made a ratiometric measurement of the signal from the in-line pressure sensor <NUM>, and no correction was needed for gain and offset. The raw output of the analog-to-digital converter U4 was multiplied by a constant that was determined by the gain of the Merit MER200, which was pre-calibrated and adjusted during manufacturing. Resistors R14 and R15 of the circuit <NUM> provided mitigation for possible broken sensor leads for the in-line pressure sensor <NUM>. In the event of a breakage, the pressure reading from the analog-to-digital converter U4 was driven to an upper or lower extreme and thus became invalid.

The data from the analog-to-digital converter U4 were sent to the microprocessor U3 over a serial peripheral interface (SPI) serial channel. The data from the analog-to-digital converter U4 were assembled in <NUM> bytes which were re-assembled in the microprocessor U3 as a <NUM>-Bit word representing the catheter <NUM>/needle pressure.

The microprocessor U3 maintained some data in non-volatile memory which included a device serial number, catheter gain correction, and general hardware settings. This data could be transferred to and changed by commands sent from the display device <NUM>. This information was stored in EEPROM memory internal to the microprocessor U3.

While gathering the in-line pressure sensor data from the analog-to-digital converter U4, the microprocessor U3 also attempted to measure the cardio-induced pulse rate, if present, in the waveform signal from the in-line pressure sensor <NUM>. An average value was calculated for the waveform signal and subtracted from the raw data to provide a zero-centered waveform. The zero-centered waveform was processed to identify zero-crossings in the zero-centered waveform from which the period of the peaks and valleys was determined. A measurement of the period from the peaks/valleys was made and converted into a beats-per-minute numeric value. The numeric value and the positive zero-crossing information was passed via a communication channel to the display device <NUM>. Additional details on the operation of microprocessor U3 are discussed below in connection with <FIG>.

As shown in <FIG>, crystal Y1 was the clock source for microprocessor U3. The internal timing measurements and communication rate were established from this frequency choice. The frequency was chosen to provide sufficient computational speed while reducing radiated emission from the circuit <NUM>. The <NUM> volt battery BT1 voltage also helped mitigate emissions. Voltage dividers consisting of R1/R2 and R9/R10 scaled the voltage from battery BT1 and radio transceiver U2 to a value in the range of the analog-to-digital converter internal to microprocessor U3 and allowed measurement of the supply voltages. This design was capable of operating with battery voltages below <NUM> volts. Over <NUM> hours of continuous operation was possible before battery recharging was required.

The microprocessor U3 was programmed in-circuit by attaching a standard Microchip Technologies programmer to J2. The code could be changed in-the-field as the software design included a boot-loader section. After first programming, a production jumper JP2 may have a solder connection placed across it to protect the circuit <NUM> from future programming. The jumper JP2 also improves protection against ESD events.

The circuit <NUM> included two options for communication with the display device <NUM>. When the USB cable option was used, a Future Technologies Digital International (FTDI) serial-to-USB cable <NUM>, <FIG>, was connected to jumper J1 on the "b"-side, i.e., pins b2-b7. This provided direct attachment of the cable <NUM> to serial channel <NUM> of the microprocessor U3. The USB cable option was configured as a full implementation of RS-<NUM> (TTL) using flow control CTS/RTS. The Smart USB cable <NUM> was powered by the display device <NUM> to which the USB connection was made. Power was not provided through the circuit <NUM>. At the display device <NUM>, the USB port was configured as a virtual communications serial port.

For wireless Bluetooth® communication, the FTDI cable <NUM> was removed and jumpers were placed across pins <NUM>-<NUM>, a-to-b of jumper J1. The choice of communication baud rate was selected based on the default configuration of Bluetooth® transceiver, U3. The same baud rate was used for the FTDI USB cable. This allowed the microprocessor U3 to operate without regard to whether the information and commands were transferred from the display device <NUM> via USB or Bluetooth® communications.

The radio transceiver module U2 was a microchip design that simulated serial communication to the display device <NUM> and was pre-certified to meet the requirements of the FCC and EU standards for RF performance. The Green LED D2 indicated the radio transceiver module U2 was powered while the Red LED D3 flashed during data transmission, <FIG>. The mode jumper JP1 was normally shorted and was used only for debugging purposes. Supervisory circuit U1 provided power-on and low-voltage shutdown of the radio transceiver module U2. The display device <NUM> was responsible for pairing and bonding to the transceiver antenna AE1 of the radio transceiver module U2. Operation of the transceiver U2 occurred according to the frequencies and protocols defined for Bluetooth® BLE. The radio transceiver module U2 was defined as a server device providing data to a slave. The radio transceiver module U2 wirelessly communicated with the display device <NUM>, in the case of the prototype a tablet (Dell® Latitude <NUM>, <NUM>-in-<NUM> tablet), which executed the software for analyzing and displaying the signals from the two sensors <NUM>, <NUM>.

Turning to the display device <NUM> and signal analysis in more detail, the display device <NUM>, working alone or in concert with the controller device <NUM>, may produce useful data and alerts to the clinician to aid in the placement of the needle <NUM> and/or catheter <NUM>, including providing an indication of patency of the catheter <NUM>, <FIG>, <FIG> schematically illustrates an actual screenshot provided on the display device <NUM> as used with the working prototype <NUM> of <FIG>, which included the controller device <NUM> with controller circuit <NUM>. <FIG> provides but one exemplary output configuration for data in accordance with the present invention.

With reference to <FIG>, a display <NUM> on an LCD screen of the display device <NUM> included two graphs. The upper half of the screen displayed an "Objective Pressure Graph" <NUM> and in the lower half displayed a "Pressure Waveform Graph," <NUM> showing waveforms <NUM>, <NUM> corresponding to data collected from the sensors <NUM>, <NUM>, respectively. In addition, a Dialogue Bar was provided below the Pressure Waveform Graph. These two graphs can be shown simultaneously or can be displayed individually at different times.

The objective pressure was displayed in both the Objective Pressure Graph showing a scrolling graph of objective pressure vs. time <NUM> and as a real-time numeric value <NUM>, <FIG>. A Maximum Pressure Line was also displayed, which could be changed by the clinician. When the objective pressure exceeded this line, an audible alert was sounded, though it is understood that the audible alert could have been a visual or some other type of alert. The objective pressure <NUM> corresponded to pressure generated by the handheld syringe <NUM> as the clinician applied a force to the plunger of the syringe <NUM>. The graphing of the objective pressure data was performed on a continuous basis and in real-time, and the scaling could be changed by pressing the Up and Down arrows (↑, ↓) on the left-hand side bar of the Objective Pressure Graph <NUM>, which allowed scaling to be changed in real-time. If the pressure detected reached the Maximum Pressure Line without the expression of fluid, the clinician could conclude that the needle <NUM> and/or catheter <NUM> is occluded. A negative slope in the Objective Pressure Graph could indicate a dissipation of the pressure in the needle <NUM> and/or catheter <NUM>, further indicating that the needle <NUM> and/or catheter <NUM> was not occluded. Thus, the real-time changes in the Objective Pressure Graph provide vital information to confirm or rule out an occluded needle <NUM> or catheter <NUM> even when the data from the waveforms <NUM>, <NUM> are ambiguous. Therefore, the Objective Pressure Graph provides needle or catheter patency information in addition to the information displayed in waveforms <NUM>, <NUM>.

As to the Pressure Waveform Graph <NUM>, the waveforms <NUM>, <NUM> were constructed using a high resolution, high-speed sampling algorithm in which between <NUM> to <NUM> samplings per second were taken. In the prototype, average values of the waveforms <NUM>, <NUM> were calculated and drawn to the display device <NUM> to maintain the waveforms <NUM>, <NUM> centered on the Pressure Waveform Graph. Within <NUM> seconds (or some other programmed period of time in the software), the displayed waveform <NUM>, <NUM> was calculated to a mean pressure value and positioned to be centered within the graph <NUM> relative to the mean horizontal line <NUM> displayed in <FIG>.

The waveforms <NUM>, <NUM> from the first and second sensors <NUM>, <NUM> had peak-to-peak crests (and zero crossings) that were reflective of the pulsatile nature of the heart contracting and were consistent with the value of the number of heart beats-per-minute (bpm). The heart rate in beats-per-minute could also be calculated from the zero crossings. However, two zero-crossings are present per beat, so either time between successive positive-slope zero crossings or time between successive negative-slope zero crossings were indicative of heart rate. The two waveforms <NUM>, <NUM> could be visually compared on the display <NUM> by the clinician. In addition, a real-time numerical value <NUM> for the heart rate detected by the first sensor <NUM> was displayed, as well as the real-time numerical value <NUM> for the heart rate detected by the second sensor <NUM>, <FIG>. The detection of a both waveforms <NUM>, <NUM> from the two input sources <NUM>, <NUM> provides the clinician with an understanding as to the position of the needle <NUM> and/or catheter <NUM> within an anatomic structure that transmits a pulse wave from the cardiovascular system. Two sets of up and down arrows (↑, ↓) on the left-hand side bar of the Pressure Waveform Graph were usable to scale the heights of each of the waveforms <NUM>, <NUM> individually. In addition, an audible bpm beep could be provided which sounds with the same frequency as the pulse rate shown in either waveform <NUM> or waveform <NUM>. In such a case display of the waveforms <NUM>, <NUM> associated with the audible bpm beep could be omitted, with the audible bpm beep filling the role of providing such information to the clinician.

Alternatively, the waveforms <NUM>, <NUM> could be displayed in a variety of different formats. Exemplary formats may include,(and are not limited to): a continuous waveform which may be represented as a pressure waveform with peak-to-trough continuous line; a non-continuous line in which the peak-to-peak is displayed; or, a blinking light that is representative of the peak-to-peak pressure values that are detected by the input sources. In addition, it may be that the waveforms <NUM>, <NUM> are not both displayed but only a visual alert is provided confirming that the signals are coordinated with the peak-to-peak signal representative of heart beats-per-minutes from the two independent sources <NUM>, <NUM>. For instance it is possible that neither of the waveforms <NUM>, <NUM> are displayed, and that the peak-to-peak signals are represented as an audible or haptic signal. Or it is possible to rely solely upon the numeric values displayed as beats-per-minute. Further, any combination of these display techniques may be used.

As shown in <FIG> the Dialogue Bar included (from left to right): <NUM>) a "Zero" button to calibrate the in-line pressure sensor <NUM>; <NUM>) an objective pressure value <NUM> for the in-line pressure sensor <NUM>; <NUM>) heart rate beats-per-minute (bpm), <NUM> from the in-line pressure sensor <NUM>; <NUM>) a "Sync alert" <NUM> indicating that the heart rate values <NUM>, <NUM> were correlated to confirm that a single source (the heart) has produced both of these signals; <NUM>) a heart rate beats-per-minute (bpm) <NUM> from the finger pulse sensor <NUM>; <NUM>) an oxygen saturation value <NUM> in percent; and <NUM>) an "^image^" button to capture the image on the screen.

The display device <NUM> in the prototype performed an analysis to determine whether the two waveforms <NUM>, <NUM> were correlated at their fundamental frequency, which frequency corresponded to the cardiac bpm (beats-per-minute) if the waveform <NUM>, <NUM> represented the cardiac pulsewave. If not, the fundamental frequency would correspond to some other spurious signal not related to the cardiovascular system. Two signals were considered correlated in frequency even if a phase offset between the two signals were present, such as illustrated in the waveforms <NUM>, <NUM>, <FIG>. A phase offset between the signals may be present due to the fact that the cardiac pulse may travel through different tissue types and different distances to arrive at each of the sensors <NUM>, <NUM>.

If the waveforms <NUM>, <NUM> were frequency-correlated, the "Sync alert" <NUM> would flash on/off to alert the clinician that the bpm rates from each of the sensors <NUM>, <NUM> were found to be correlated, i.e., that the frequency of signals from the sensors <NUM>, <NUM> were sufficiently matched within a selected deviation, with an acceptable range of deviation of <NUM> bpm to <NUM> bpm. Thus, the clinician was provided with a confirmation of location of the needle <NUM>/catheter <NUM> at the desired location when the "Sync alert" <NUM> was activated. In addition, an alert may optionally be sounded if the two waveforms <NUM>, <NUM> were not correlated, indicating that the needle <NUM> and/or the catheter <NUM> was not positioned properly. Any of these alerts may be visual, audible, haptic, or any combination thereof.

The signals detected by the sensors <NUM>, <NUM> may also be analyzed by a variety of correlation techniques to determine the cardiac pulse rate, including but not limited to, waveform analysis, pulse-rate comparison (heart-rate, beats-per-minute), cross-correlation, and combinations thereof. In yet another embodiment a cross-correlation analysis may be performed on the data from the sensors <NUM>, <NUM> producing a matched frequency of the two signals with time-shift producing definitive positive correlation based on set a criteria. In this case, the cross-correlation may be the sum of the product of the two signals shifted relative to each other over a period of not less than one complete cycle of the longer period waveform. In yet another embodiment auto-correlation may be used to normalize the values for better threshold detection comparison of the cross-correlation peak value. In yet another embodiment the auto-correlation peak spacing can be used to verify the validity of the BPM measurements made of each sensor data.

In yet another embodiment a cross-correlation analysis may be performed on the data from the two input sources <NUM>, <NUM> producing a definitive positive correlation based on set criteria. Illustrated in <FIG> is an example of a cross-correlation technique in accordance with the present invention that may be used to objectively determine the degree of correlation of the two signals <NUM>, <NUM> from sensors <NUM>, <NUM>. Exemplary details are specific to an implementation for the controllers <NUM> and <NUM>. For discrete data samples as collected by exemplary devices <NUM>, <NUM> of the present invention, the cross-correlation function may be defined as <MAT> where T is the period (number of samples) of the waveform being analyzed, and τ is the sliding offset between the two waveforms.

Basically, the correlation function generates a series of sum-of-products over the entire sampled data set to come up with values of the correlation coefficient for each τ value. The correlation coefficients calculated have a maximum value at shift τmax. Due to possible velocity propagation delays through the patient tissue, the two waveforms <NUM>, <NUM> may have an offset in the peak correlation coefficient position, in which is τmax ≠ <NUM>. The method <NUM> shown in <FIG> presents a representation of an exemplary method which may be used for correlation detection in accordance with the present invention. The collected data from the the in-line pressure sensor <NUM> is input at step <NUM>. The pressure reading from the finger-sensor <NUM> is input at step <NUM>. The data are collected synchronously by display device <NUM>, and hence the pair of data (<NUM>, <NUM>) represents a single instance in time. The sampled data are placed in circular FIFO buffers <NUM>, <NUM>. The size of the buffers <NUM>, <NUM> is determined by the period of the pulsewaves <NUM>, <NUM>. The longest period occurs at the lowest pulse rate which is defined to be <NUM> BPM. With a data sampling frequency of <NUM> samples/second, a minimum of <NUM> samples represent one complete wave form in each buffer <NUM>, <NUM>. In addition, the τ shift could be up to <NUM> samples as well. Hence, the minimum buffer size to perform a complete cross-correlation function is <NUM> for the combined buffers <NUM>, <NUM>. In this exemplary case, the buffer length may be chosen as <NUM>, which makes circular FIFO buffer management easier and also provides some addition space in the buffers <NUM>, <NUM>. An extra <NUM> buffer positions of padding (<NUM>-<NUM>=<NUM>) may be provided that allow new data to be inserted into the circular buffers <NUM>, <NUM> without corrupting the <NUM> values being processed to determine the correlation coefficients. The buffers <NUM>, <NUM> may be simultaneously written and read which eases the computational burden on the microprocessor in the display device <NUM>. The computation need not be completed in a single data sample time. Real word correlation is generally a serial process of mathematical operations. Each new correlation check is begun at the position of the last data written to the circular buffers <NUM>, <NUM> and works backwards.

The correlation algorithm <NUM> may begin at the last data position written and work backwards through the data from this point. Based on the values of buffer size and assumed pulse rates, the complete computation must finish before <NUM> additional data samples are taken, that is: <NUM> samples / <NUM> samples/second, or <NUM> seconds. In this time <NUM> sum-of-products are calculated. The sum-of-product, step <NUM>, is the accumulation of <NUM> multiplications 910a-910d of data in each buffer <NUM>, <NUM>. Each correlation coefficient calculated at summation point <NUM> may be temporarily stored in an array buffer <NUM>. Each value saved is the sum-of-product for <NUM> offsets of the τ parameter. The τ offset is the starting from which data is read from the buffers <NUM>, <NUM> for each sum-of-product calculation. The array buffer <NUM> results may be analyzed to determine the degree of correlation between the pulsewaves. To normalize the cross-correlation results, auto-correlation may also be performed. Numerically, the cross-correlation results in buffer <NUM> should be values between +<NUM> and -<NUM>. Values near <NUM> are considered to be non-correlated and indicated as not "In-Sync" on the display device <NUM>. Values greater than a determined threshold are considered significantly correlated and provide an indication to the clinician of correct placement of the needle <NUM> and/or catheter <NUM>. Should the pulse rate be greater than the minimum design value, multiple correlation coefficients will be produced. For example, at <NUM> BPM pulse rate, there will be <NUM> correlation maximums. The correlation algorithm <NUM> may analyze the data for maximum peak and generally select the τ offset value closer to zero. All of the selected correlation coefficients may be output to the display device <NUM>. The analysis may include consideration of the measured BPM from each sensor <NUM>, <NUM>. BPM may also be obtained by analysis of the auto-correlation measurements made on each waveform <NUM>, <NUM>. Though possibly lacking in resolution detail, the separation measurement of multiple peaks in auto-correlation may be another measurement of pulse rates from each sensor <NUM>, <NUM> and maybe useful information for making the correlation detection indication.

Devices disclosed herein may use the method <NUM> in confirming catheter or needle placement and patency, <FIG>. The flowchart of <FIG> represents the software logic that was used in the prototype to calculate the beats-per-minute pulse rate as measured by the in-line pressure sensor <NUM>. The software executed in the microprocessor U3, <FIG>, of circuit <NUM> of the controller device <NUM>. The software identified the zero-crossings of the cardiac pulsewave signal <NUM> in the needle <NUM> and/or catheter <NUM>, <FIG>. The beats-per-minute rate was determined by measuring the period of time between successive positive zero-crossings of the pulsewave signal <NUM>. The positive zero-crossings were selected, because the ascending aortic systolic pressure wave has a faster rate of change and hence provides a more accurate point of measurement than the descending slope of the negative zero-crossings. The software operated in a loop <NUM> using a state machine to analyze the pulsewave <NUM>.

The state machine was initialized at step <NUM> when software began executing, <FIG>. The STATE variable determined which side of the mean average the loop <NUM> was last processing. A Filter Counter variable was provided which was incremented and decremented based on whether the difference between measured value and the mean average was above or below zero. The Running Average Filter was also initialized at step <NUM>. At step <NUM>, the pressure reading was obtained from the analog-to-digital converter U4 of <FIG>. Analog-to-digital conversions were produced by hardware events and occurred at approximately <NUM> samples per second. A new value of the pressure sample was obtained at step <NUM> and was sent to the display device <NUM>. The new pressure sample was also used in method <NUM>. Specifically, the new pressure sample was added into the Running Average Filter by computing the running average at step <NUM>. The Running Average Filter output a value which was the average of the last <NUM> pressure samples. At step <NUM> the pressure sample had the average value subtracted to generate the Difference value which was stored at step <NUM>. Next, a decision was made at step <NUM> to determine if last previous operation was looking for a positive (POS) or negative (NEG) zero-crossing. If the STATE at step <NUM> was POS, then the software branched to step <NUM> looking for a negative crossing. The criterion for a negative crossing was that the Difference was less (more negative) than a negative threshold of - <NUM> mmHg. If the Difference did not meet this criterion, then the loop passed to step <NUM> where it waited for the next pressure sample to repeat, via step <NUM>, the processing of method <NUM>. Returning to step <NUM>, should the Difference meet the criterion, then the Filter Counter was decremented, step <NUM>. At step <NUM> the count value was tested to determine if the count was less than -<NUM>. If not, control passed to step <NUM> and method <NUM> repeated by passing to step <NUM> and waiting for the next sample. Normally the last value of the Filter Counter would be +<NUM> following the last positive zero-crossing. Hence the Filter Counter must be decremented <NUM> times to reach the value -<NUM> tested, and the STATE variable was then set to NEG indicating that a descending zero-crossing was found, step <NUM>. The Filter Counter value was forced such that it does not exceed -<NUM>. The loop <NUM> then returned to wait for the next pressure sample at step <NUM>.

Returning to step <NUM>, if the STATE at step <NUM> was NEG (i.e., not POS), that is looking for an ascending zero-crossing, the branch would continue to step <NUM>. At step <NUM> a test was made to determine if the criterion for a positive zero-crossing was met. The Difference pressure must exceed +<NUM> mmHg. If not, the method <NUM> repeated jumping to step <NUM> and waited for another pressure sample. Should the criterion be met, control passed to step <NUM>. The Filter Counter value was incremented at step <NUM>. Typically the counter would begin incrementing from -<NUM> after the last descending zero-crossing. At step <NUM> the count value was tested to determine if sufficient positive differences had been found to justify indication of an ascending zero-crossing of pressure, that is that the count exceeded +<NUM>. If not, control passed to step <NUM> and method <NUM> repeated by passing to step <NUM> and waiting for the next sample. Should the Filter Counter exceed +<NUM> at step <NUM>, then control passed to step <NUM>. At step <NUM> the STATE variable was set to POS and the Filter counter was limited to +<NUM>. At this point a valid positive zero-crossing had been determined. An algorithm measured the period of time since the last positive zero-crossing occurred. The period was measured in milliseconds by a time base maintained in microprocessor U3 using interrupts. The period measurement was dynamically adjusted to provide good BPM measurements. At fast heart rates greater than <NUM> BPM, up to <NUM> zero-crossings are counted to give a resolution better than <NUM> BPM. At low pulse rates, below <NUM> BPM, a single zero-crossing period measurement was performed to allow quicker updates of the measured heart rhythm. The final calculation of period was performed at step <NUM> and the calculated BPM value, <NUM> in <FIG>, was sent to the process controller <NUM> for display to the user and for pulse correlation matching with the heart rate <NUM>.

A further understanding of how the devices <NUM>, <NUM> of the present invention may operate with regard to generating the data for display on the display device <NUM> is seen in the block diagram <NUM> of <FIG>. In this diagram, the "cardiovascular pulse sensor device" block corresponds to the sensor <NUM> and the "pressure sensor device" block corresponds to the sensor <NUM>. Communication among the components and processes is illustrated as wireless using the conventional symbol for Bluetooth® communication, though the components and processes could communicate via other methods such as Wi-Fi or hard wired.

The application software <NUM>, which can run on the display device <NUM>, can include the step <NUM> for writing a time/date stamp to the sensor <NUM> to assist in ensuring that the sensor <NUM> is used for only a single use. As part of the operation, the software also obtains the data from the sensors <NUM>, <NUM> at step <NUM>. Collection of data continues until complete, step <NUM>, and the Bluetooth® radio is disabled, step <NUM>. During the data collection step <NUM> a sub process <NUM> can run which includes functions such as creating the graphical display of the pressure <NUM>; calculating the excessive pressure alert <NUM>; displaying the numerical pressure <NUM>; performing the correlation detection of the data received from the sensors <NUM>, <NUM>, step <NUM>; and, issuing the various alerts <NUM>.

In addition, an authorization scheme of the present invention may include a computer chip, SIM, or other uniquely coded circuit in the adapter <NUM> or sensor <NUM>, for example chip <NUM>. The chip, SIM, or other uniquely coded circuit may be disposed in communication with the controller device <NUM> and/or display device <NUM>, and may be read by an authorization program or circuit in the controller and/or display device <NUM>, <NUM>. If the chip, SIM, or other uniquely coded circuit is genuine, the controller and/or display device <NUM>, <NUM> will operate properly, if not, the sensor <NUM> may be disabled and a warning such as "unauthorized adaptor detected" can be posted on the display device <NUM> and optionally a warning sound may be made, including but not limited to a vocalization of words, an alarm, or other warning signal or any combination thereof. The coded circuit may also be coded for a one-use function whereby the authorization program or circuit in controller and/or display device <NUM>, <NUM> will detect if a specific sensor <NUM> was previously used and, if so, again disable the controller and/or display device <NUM>, <NUM> and post a warning.

Devices disclosed herein may provide the clinician with a particularly useful method of confirming catheter or needle placement and patency, such as the method <NUM> illustrated in <FIG>. For example, the clinician often needs to determine if a catheter is: i) clogged or functioning and/or ii) if the catheter has moved from the target position, collectively beginning at step <NUM>. Making such a determination may necessitate the following actions: <NUM>) flush the catheter to determine if it is clogged or clear and then <NUM>) infuse a bolus of drug. In making such a determination, the clinician may connect an in-line pressure sensor between the catheter and a syringe used to flush the catheter, step <NUM>, and may attach a secondary input source to detect a heartbeat, such as a photophelthysmography fingertip clamshell to detect the heartbeat. The syringe and in-line pressure sensor, and any other disposables such as a catheter, may be primed with fluid, step <NUM>. The in-line pressure sensor and secondary source may be operably connected, wired or wirelessly, to a display device for viewing by the clinician, step <NUM>. A maximum objective pressure value may also be set on the handheld device and remain stored in the handheld device for future use. The maximum pressure value may be set anywhere between <NUM>/Hg to <NUM>/Hg, for example. When the maximum pressure value is reached an alert may be sounded as an audible sound or tone. A spoken word may also be used to alert the clinician that the maximum pressure has been exceeded.

Signals from the in-line pressure sensor and secondary source (e.g., a finger pulse sensor) may be compared and analyzed by a controller and/or display device, such as one or more of the controller <NUM> and display device <NUM>. If the two signals are found to be correlated in frequency (that is beats-per-minute of a heartbeat), an alert may be displayed on the display device as a flashing box and/or an audible alert sounded, indicating that the catheter is properly positioned.

If a pulsewave is detected, step <NUM>, the clinician may proceed with flushing the catheter, step <NUM>. The clinician may again observe the response on the display device, step <NUM>. If no response is observed and no pulsewave correlation is found between the signal from the in-line pressure sensor and the secondary input source, step <NUM>, the pulsewave detected at step <NUM> (or step <NUM> as described below) is a false-positive finding. The clinician then concludes that the catheter is not properly positioned, and the catheter is removed, step <NUM>. Alternatively, if a response is observed at step <NUM>, and the clinician observes that pulsewave correlation is found between the signal from the in-line pressure sensor and the secondary input source, step <NUM>, the clinician can bolus the patient with the drug, step <NUM>, and observe the therapeutic output, step <NUM>.

Returning to the situation where no initial response is observed at step <NUM>, the clinician may observe the objective pressure graph to determine patency of the catheter. In such a case the clinician will likely see that no pulsewave is detected at all, step <NUM>, but will still proceed with flushing the catheter, step <NUM>. Again, the clinician may observe the response on the display device, step <NUM>. The clinician may then determine if the catheter is clogged by observing an absence of a gradual reduction in the pressure; this may be observed by viewing an objective pressure vs. time graph in which the slope of the curve demonstrates whether fluid is flowing out of the catheter and into the tissues. If the pressure does not dissipate over time, step <NUM>, and no pulsewave correlation is found between the signal from the in-line pressure sensor and the secondary input source, step <NUM>, the clinician can conclude that the catheter is clogged and the catheter may be removed, step <NUM>. Alternatively, if a response is observed at step <NUM> and the response is a reduction of pressure, step <NUM>, the clinician may observe that pulsewave correlation is found between the signal from the in-line pressure sensor and the secondary input source, step <NUM>. In such a case, the clinician may proceed with flushing the catheter, step <NUM>, and may proceed with steps <NUM> through <NUM> as described above. The example in the proceeding sections describe the method for use with a catheter, it is understood that a similar method could be used for placement of a needle within a patient performed with the same steps described.

It is anticipated that the method <NUM> could be used for confirmation of the position of a catheter in the epidural space or the intrathecal space, for example. In addition, the method <NUM> could be used to determine when a needle or catheter is positioned properly in a vessel such as a vein or artery for an infusion. It is also conceivable that such a system could be used for aspiration of bodily fluids in which the needle position within a target confirmed by a pulsatile waveform is necessary prior to the removal of said fluid such as cerebral spinal fluid from the central nervous system. The method <NUM> may also be used in situations where assessing the pulsatile nature of a tissue is vital. Devices and methods of the present invention may also be used to assess the perfusion status of vessels to a tissue or organ based on the quality (amplitude and cadence) of the pulsatile pressure waveform as seen in the pulse interval and amplitude of the waveform curve; for example, the perfusion status may be assessed in the extremities as it relates to diabetes, frost-bite, trauma, tissue grafting, etc..

Thus, the above disclosure describes devices and methods that can confirm the location of a needle and/or catheter as well as the patency of properly located indwelling catheter. The devices and methods may provide essential confirmation through physiologic feedback that a needle or catheter has been positioned within an anatomic site. Devices in accordance with the present invention may detect the presence of cardiovascular signals from two separate input sources and determine if the signals are coordinated or not by analysis of the signals. A positive-correlation may be confirmed, verifying the position of a needle or catheter within the body and an alert may be provided in response. If a correlation cannot be established between the two cardiovascular signals, no alert is provided, which indicates that a needle and/or catheter is improperly positioned.

Claim 1:
An apparatus (<NUM>, <NUM>) for confirming placement of a hollow-bore structure (<NUM>, <NUM>) at a desired treatment location in a mammalian subject (<NUM>), comprising:
A first sensor (<NUM>) operably connected to a lumen disposed in the hollow-bore structure, the first sensor configured to provide a first signal in response to detection of a first property indicative of a cardiac pulse in the lumen of the hollow-bore structure, the hollow-bore structure optionally comprising one or more of a needle and a catheter;
a second sensor (<NUM>) configured to provide a second signal in response to detection of a second property indicative of the cardiac pulse, the second sensor optionally comprising a finger pulse sensor; and
a controller (<NUM>, <NUM>) operably connected (<NUM>, <NUM>, <NUM>) to the first and second sensors to receive the first and second signals, the controller optionally disposed in wireless communication with one or more of the first and second sensors,
characterised in that the controller is configured to compare the first and second signals to provide a comparison result, whereby the comparison result provides an indication of placement of the hollow-bore structure relative to the desired treatment location.