U.S. patent application number 13/950686 was filed with the patent office on 2013-11-21 for system and method for determining the point of hydration and proper time to apply potential to a glucose sensor.
This patent application is currently assigned to MEDTRONIC MINIMED, INC.. The applicant listed for this patent is MEDTRONIC MINIMED, INC.. Invention is credited to David Y. Choy, Kenneth W. Cooper, Rajiv Shah, Gopikrishnan Soundararajan, Ratnakar Vejella.
Application Number | 20130311103 13/950686 |
Document ID | / |
Family ID | 40551241 |
Filed Date | 2013-11-21 |
United States Patent
Application |
20130311103 |
Kind Code |
A1 |
Cooper; Kenneth W. ; et
al. |
November 21, 2013 |
System and Method for Determining the Point of Hydration and Proper
Time to Apply Potential to a Glucose Sensor
Abstract
According to an embodiment of the invention, a method of
determining hydration of a sensor having a plurality of electrodes
is disclosed. In particular embodiments, the method couples a
sensor electronics device to the sensor and measures the open
circuit potential between at least two of the plurality of
electrodes. Then, the open circuit potential measurement is
compared to a predetermined value. In some embodiments, the
plurality of electrodes includes a working electrode, a reference
electrode, and a counter electrode. In still further embodiments,
the open circuit potential between the working electrode and the
reference electrode is measured. In other embodiments, the open
circuit potential between the working electrode and the counter
electrode is measured. In still other embodiments, the open circuit
potential between the counter electrode and the reference electrode
is measured.
Inventors: |
Cooper; Kenneth W.;
(Newhall, CA) ; Choy; David Y.; (San Gabriel,
CA) ; Shah; Rajiv; (Rancho Palos Verdes, CA) ;
Soundararajan; Gopikrishnan; (Irvine, CA) ; Vejella;
Ratnakar; (Irvine, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
MEDTRONIC MINIMED, INC. |
Northridge |
CA |
US |
|
|
Assignee: |
MEDTRONIC MINIMED, INC.
Northridge
CA
|
Family ID: |
40551241 |
Appl. No.: |
13/950686 |
Filed: |
July 25, 2013 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
13328472 |
Dec 16, 2011 |
|
|
|
13950686 |
|
|
|
|
11966294 |
Dec 28, 2007 |
8114269 |
|
|
13328472 |
|
|
|
|
11323242 |
Dec 30, 2005 |
|
|
|
11966294 |
|
|
|
|
Current U.S.
Class: |
702/19 |
Current CPC
Class: |
G01N 27/3271 20130101;
A61B 5/14532 20130101; A61B 5/6849 20130101; A61B 17/3468 20130101;
A61B 5/14865 20130101; A61B 2560/0223 20130101; A61B 5/6848
20130101 |
Class at
Publication: |
702/19 |
International
Class: |
A61B 5/145 20060101
A61B005/145 |
Claims
1. A program code storage device, comprising: a machine-readable
medium; and machine-readable program code, stored on the
machine-readable medium, the machine-readable program code
including instructions, which when executed cause a processor for a
sensor electronics device that is operably coupled to a sensor
having a plurality of electrodes to: receive measurements of
successive open circuit potential values between at least two of
the plurality of electrodes; calculate the rate of change of the
measured open circuit potential values as the change over time
between an open circuit potential value measured earlier in time
and an open circuit potential value measured later in time; compare
the open circuit potential values and the calculated rate of change
to respective predetermined thresholds; determine that the sensor
is ready for use if said predetermined thresholds are met; repeat,
over a specified period of time, the measuring, calculating, and
comparing steps if said predetermined thresholds are not met; and
if said predetermined thresholds are not met after the specified
period of time has been exceeded, determine that the sensor is not
useable.
2. The program code storage device of claim 1, wherein the
plurality of electrodes includes a working electrode, a reference
electrode, and a counter electrode.
3. The program code storage device of claim 2, wherein said
measurements are for open circuit potential values between the
working electrode and the reference electrode.
4. The program code storage device of claim 2, wherein said
measurements are for open circuit potential values between the
working electrode and the counter electrode.
5. The program code storage device of claim 2, wherein said
measurements are for open circuit potential values between the
counter electrode and the reference electrode.
6. The program code storage device of claim 2, wherein said
measurements are for open circuit potential values between the
working electrode and the reference electrode and between the
counter electrode and the reference electrode.
7. The program code storage device of claim 2, wherein said
measurements are for open circuit potential values between the
working electrode and the counter electrode and between the counter
electrode and the reference electrode.
8. The program code storage device of claim 2, wherein said
measurements are for open circuit potential values between the
working electrode and the reference electrode, between the working
electrode and the counter electrode, and between the counter
electrode and the reference electrode.
9. The program code storage device of claim 1, wherein said
plurality of electrodes are configured to be placed percutaneously
or subcutaneously at a selected site in a body of a user.
10. A program code storage device, comprising: a machine-readable
medium; and machine-readable program code, stored on the
machine-readable medium, the machine-readable program code
including instructions, which when executed cause a processor of a
hydration detection circuit that is operably coupled to a sensor
having a plurality of electrodes to: receive measurements of
successive open circuit potential values between at least two of
the plurality of electrodes; calculate the rate of change of the
measured open circuit potential values as the change over time
between an open circuit potential value measured earlier in time
and an open circuit potential value measured later in time; compare
the open circuit potential values and the calculated rate of change
to respective predetermined thresholds; determine that the sensor
is hydrated if said predetermined thresholds are met; repeat, over
a specified period of time, the measuring, calculating, and
comparing steps if said predetermined thresholds are not met; and
if said predetermined thresholds are not met after the specified
period of time has been exceeded, determine that the sensor will
not hydrate.
11. The program code storage device of claim 10, wherein the
plurality of electrodes includes a working electrode, a reference
electrode, and a counter electrode.
12. The program code storage device of claim 11, wherein said
measurements are for open circuit potential values between the
working electrode and the reference electrode.
13. The program code storage device of claim 11, wherein said
measurements are for open circuit potential values between the
working electrode and the counter electrode.
14. The program code storage device of claim 11, wherein said
measurements are for open circuit potential values between the
counter electrode and the reference electrode.
15. The program code storage device of claim 11, wherein said
measurements are for open circuit potential values between the
working electrode and the reference electrode and between the
counter electrode and the reference electrode.
16. The program code storage device of claim 11, wherein said
measurements are for open circuit potential values between the
working electrode and the counter electrode and between the counter
electrode and the reference electrode.
17. The program code storage device of claim 11, wherein said
measurements are for open circuit potential values between the
working electrode and the reference electrode, between the working
electrode and the counter electrode, and between the counter
electrode and the reference electrode.
18. The program code storage device of claim 10, wherein said
plurality of electrodes are configured to be placed percutaneously
or subcutaneously at a selected site in a body of a user.
Description
RELATED APPLICATIONS
[0001] This is a divisional application of U.S. patent application
Ser. No. 13/328,472, filed Dec. 16, 2011, now U.S. Pat. No. ______,
which is a continuation of U.S. patent application Ser. No.
11/966,294, filed Dec. 28, 2007, now U.S. Pat. No. 8,114,269, which
is a continuation-in-part application of U.S. patent application
Ser. No. 11/323,242, filed Dec. 30, 2005, all of which are
specifically incorporated by reference herein.
FIELD OF THE INVENTION
[0002] Embodiments of this invention relate generally to methods
and systems for hydration of sensors. More particularly,
embodiments of this invention relate to systems and methods for
determining the point of hydration of a sensor and the proper time
to apply potential to the sensor, in order for the sensor to
provide accurate readings of a physiological condition of a
subject.
DESCRIPTION OF RELATED ART
[0003] Subjects and medical personnel wish to monitor readings of
physiological conditions within the subject's body. Illustratively,
subjects wish to monitor blood glucose levels in a subject's body
on a continuing basis. Presently, a patient can measure his/her
blood glucose (BG) using a BG measurement device, such as a test
strip meter, a continuous glucose measurement system, or a hospital
hemacue. BG measurement devices use various methods to measure the
BG level of a patient, such as a sample of the patient's blood, a
sensor in contact with a bodily fluid, an optical sensor, an
enzymatic sensor, or a fluorescent sensor. When the BG measurement
device has generated a BG measurement, the measurement is displayed
on the BG measurement device.
[0004] Current continuous glucose measurement systems include
subcutaneous (or short-term) sensors and implantable (or long-term)
sensors. For each of the short-term sensors and the long-term
sensors, a patient has to wait a certain amount of time in order
for the continuous glucose sensor to stabilize and to provide
accurate readings. In many continuous glucose sensors, the subject
must wait three hours for the continuous glucose sensor to
stabilize before any glucose measurements are utilized. This is an
inconvenience for the patient and in some cases may cause the
patient not to utilize a continuous glucose measurement system.
[0005] Further, when a glucose sensor is first inserted into a
patient's skin or subcutaneous layer, the glucose sensor does not
operate in a stable state. The electrical readings from the sensor,
which represent the glucose level of the patient, vary over a wide
range of readings. In the past, sensor stabilization used to take
several hours. A technique for sensor stabilization is detailed in
U.S. Pat. No. 6,809,653, ("the '653 patent"), application Ser. No.
09/465,715, filed Dec. 19, 1999, issued Oct. 26, 2004, to Mann et
al., assigned to Medtronic Minimed, Inc., which is incorporated
herein by reference. In the '653 patent, the initialization process
for sensor stabilization may be reduced to approximately one hour.
A high voltage (e.g., 1.0-1.2 volts) may be applied for 1 to 2
minutes to allow the sensor to stabilize and then a low voltage
(e.g., between 0.5-0.6 volts) may be applied for the remainder of
the initialization process (e.g., 58 minutes or so). Thus, even
with this procedure, sensor stabilization still requires a large
amount of time.
[0006] It is also desirable to allow electrodes of the sensor to be
sufficiently "wetted" or hydrated before utilization of the
electrodes of the sensor. If the electrodes of the sensor are not
sufficiently hydrated, the result may be inaccurate readings of the
patient's physiological condition. In addition, insufficient
hydration may cause permanent damage to the sensor during startup
and initialization. A user of current blood glucose sensors is
instructed to not power up the sensors immediately. Some users are
told to allow for a 5 minute hydration period prior to applying
power to the sensor. If they are utilized too early, current blood
glucose sensors do not operate in an optimal or efficient fashion.
No automatic procedure or measuring technique is utilized to
determine when to power on the sensor. This manual process is
inconvenient and places too much responsibility on the patient, who
may forget to apply or turn on the power source. In addition, the
manual waiting time (e.g., 5 minutes) is burdensome in instances
where a sensor hydrates faster than the recommended hydration time.
Conversely, the manual waiting time may be too short for some
sensors to completely hydrate, thus causing damage to sensor
electrodes upon application of power from the user.
BRIEF SUMMARY OF THE INVENTION
[0007] According to an embodiment of the invention, a method of
determining hydration of a sensor having a plurality of electrodes
is disclosed. In particular embodiments, the method couples a
sensor electronics device to the sensor and measures the open
circuit potential between at least two of the plurality of
electrodes. Then, the open circuit potential measurement is
compared to a predetermined value. In some embodiments, the
plurality of electrodes includes a working electrode, a reference
electrode, and a counter electrode. In still further embodiments,
the open circuit potential between the working electrode and the
reference electrode is measured. In other embodiments, the open
circuit potential between the working electrode and the counter
electrode is measured. In still other embodiments, the open circuit
potential between the counter electrode and the reference electrode
is measured.
[0008] In yet additional embodiments, the open circuit potential
between the working electrode and the reference electrode is
measured, along with the measurement of the open circuit potential
between the working electrode and the counter electrode. In further
embodiments, the open circuit potential between the working
electrode and the reference electrode is measured, along with the
measurement of the open circuit potential between the counter
electrode and the reference electrode. In still additional
embodiments, the open circuit potential between the working
electrode and the counter electrode is measured along with the
measurement of the open circuit potential between the counter
electrode and the reference electrode. In still other embodiments,
the open circuit potential between the working electrode and the
reference electrode is measured, along with the measurement of the
open circuit potential between the working electrode and the
counter electrode, and along with the measurement of the open
circuit potential between the counter electrode and the reference
electrode. In other embodiments, the method also calculates the
rate of change of the open circuit potential measurements over a
specified period of time and, in some embodiments, compares the
rate of change value to a predetermined value.
[0009] According to another embodiment of the invention, a system
for determining the point of hydration of a sensor is disclosed.
The system includes a sensor that has a plurality of electrodes,
and a sensor electronics device that has a hydration detection
circuit. The hydration detection circuit measures the open circuit
potential between at least two of the plurality of electrodes to
determine the point of hydration of the sensor. In some
embodiments, the plurality of electrodes includes a working
electrode, a reference electrode, and a counter electrode. In
additional embodiments, the open circuit potential between the
working electrode and the reference electrode is measured. In other
embodiments, the open circuit potential between the working
electrode and the counter electrode is measured. In still further
additional embodiments, the open circuit potential between the
counter electrode and the reference electrode is measured.
[0010] In further embodiments, the open circuit potential between
the working electrode and the reference electrode is measured,
along with the measurement of the open circuit potential between
the working electrode and the counter electrode. In other
embodiments, the open circuit potential between the working
electrode and the reference electrode is measured, along with the
measurement of the open circuit potential between the counter
electrode and the reference electrode. In still additional
embodiments, the open circuit potential between the working
electrode and the counter electrode is measured, along with the
measurement of the open circuit potential between the counter
electrode and the reference electrode. In other additional
embodiments, the open circuit potential between the working
electrode and the reference electrode is measured, along with the
measurement of the open circuit potential between the working
electrode and the counter electrode, and along with the measurement
of the open circuit potential between the counter electrode and the
reference electrode. In further embodiments, the hydration
detection circuit also calculates a rate of change of the open
circuit potential measurements over a specified period of time to
determine the point of hydration of the sensor.
[0011] Other features and advantages of the invention will become
apparent from the following detailed description, taken in
conjunction with the accompanying drawings which illustrate, by way
of example, various features of embodiments of the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
[0012] A detailed description of embodiments of the invention will
be made with reference to the accompanying drawings, wherein like
numerals designate corresponding parts in the figures.
[0013] FIG. 1 is a perspective view of a subcutaneous sensor
insertion set and block diagram of a sensor electronics device
according to an embodiment of the invention;
[0014] FIG. 2A illustrates a substrate having two sides, a first
side which contains an electrode configuration and a second side
which contains electronic circuitry;
[0015] FIG. 2B illustrates a general block diagram of an electronic
circuit for sensing an output of a sensor;
[0016] FIG. 3 illustrates a block diagram of a sensor electronics
device and a sensor including a plurality of electrodes according
to an embodiment of the invention;
[0017] FIG. 4 illustrates an alternative embodiment of the
invention including a sensor and a sensor electronics device
according to an embodiment of the present invention;
[0018] FIG. 5 illustrates an electronic block diagram of the sensor
electrodes and a voltage being applied to the sensor electrodes
according to an embodiment of the present invention;
[0019] FIG. 6A illustrates a method of applying pulses during
stabilization timeframe in order to reduce the stabilization
timeframe according to an embodiment of the present invention;
[0020] FIG. 6B illustrates a method of stabilizing sensors
according to an embodiment of the present invention;
[0021] FIG. 6C illustrates utilization of feedback in stabilizing
the sensors according to an embodiment of the present
invention;
[0022] FIG. 7 illustrates an effect of stabilizing a sensor
according to an embodiment of the invention;
[0023] FIG. 8A illustrates a block diagram of a sensor electronics
device and a sensor including a voltage generation device according
to an embodiment of the invention;
[0024] FIG. 8B illustrates a voltage generation device to implement
this embodiment of the invention;
[0025] FIG. 8C illustrates a voltage generation device to generate
two voltage values, and FIG. 8D illustrates a voltage generation
device having three voltage generation systems, according to
embodiments of the invention;
[0026] FIG. 9A illustrates a sensor electronics device including a
microcontroller for generating voltage pulses according to an
embodiment of the present invention;
[0027] FIG. 9B illustrates a sensor electronics device including an
analyzation module according to an embodiment of the present
invention;
[0028] FIG. 10 illustrates a block diagram of a sensor system
including hydration electronics according to an embodiment of the
present invention;
[0029] FIG. 11 illustrates an embodiment of the invention including
a mechanical switch to assist in determining a hydration time;
[0030] FIG. 12 illustrates an electrical detection of detecting
hydration according to an embodiment of the invention;
[0031] FIG. 13A illustrates a method of hydrating a sensor
according to an embodiment of the present invention;
[0032] FIG. 13B illustrates an additional method for verifying
hydration of a sensor according to an embodiment of the present
invention;
[0033] FIGS. 14A and (b) illustrate methods of combining hydrating
of a sensor with stabilizing a sensor according to an embodiment of
the present invention; and
[0034] FIG. 14C illustrates an alternative embodiment of the
invention where the stabilization method and hydration method are
combined;
[0035] FIG. 15 illustrates a logic flowchart for open circuit
potential measurements according to an embodiment of the present
invention;
[0036] FIG. 16 plots a sample time series sequence of events in
accordance with an embodiment of the present invention.
DETAILED DESCRIPTION OF THE INVENTION
[0037] In the following description, reference is made to the
accompanying drawings which form a part hereof and which illustrate
several embodiments of the present inventions. It is understood
that other embodiments may be utilized and structural and
operational changes may be made without departing from the scope of
the present inventions.
[0038] The present invention described below with reference to
flowchart illustrations of methods, apparatus, and computer program
products. It will be understood that each block of the flowchart
illustrations, and combinations of blocks in the flowchart
illustrations, can be implemented by computer program instructions
(as can any menu screens described in the Figures). These computer
program instructions may be loaded onto a computer or other
programmable data processing apparatus (such as a controller,
microcontroller, or processor in a sensor electronics device to
produce a machine, such that the instructions which execute on the
computer or other programmable data processing apparatus create
instructions for implementing the functions specified in the
flowchart block or blocks. These computer program instructions may
also be stored in a computer-readable memory that can direct a
computer or other programmable data processing apparatus to
function in a particular manner, such that the instructions stored
in the computer-readable memory produce an article of manufacture
including instructions which implement the function specified in
the flowchart block or blocks. The computer program instructions
may also be loaded onto a computer or other programmable data
processing apparatus to cause a series of operational steps to be
performed on the computer or other programmable apparatus to
produce a computer implemented process such that the instructions
which execute on the computer or other programmable apparatus
provide steps for implementing the functions specified in the
flowchart block or blocks, and/or menus presented herein.
[0039] FIG. 1 is a perspective view of a subcutaneous sensor
insertion set and a block diagram of a sensor electronics device
according to an embodiment of the invention. As illustrated in FIG.
1, a subcutaneous sensor set 10 is provided for subcutaneous
placement of an active portion of a flexible sensor 12 (see FIG.
2), or the like, at a selected site in the body of a user. The
subcutaneous or percutaneous portion of the sensor set 10 includes
a hollow, slotted insertion needle 14, and a cannula 16. The needle
14 is used to facilitate quick and easy subcutaneous placement of
the cannula 16 at the subcutaneous insertion site. Inside the
cannula 16 is a sensing portion 18 of the sensor 12 to expose one
or more sensor electrodes 20 to the user's bodily fluids through a
window 22 formed in the cannula 16. In an embodiment of the
invention, the one or more sensor electrodes 20 may include a
counter electrode, a working electrode, and a reference electrode.
After insertion, the insertion needle 14 is withdrawn to leave the
cannula 16 with the sensing portion 18 and the sensor electrodes 20
in place at the selected insertion site.
[0040] In particular embodiments, the subcutaneous sensor set 10
facilitates accurate placement of a flexible thin film
electrochemical sensor 12 of the type used for monitoring specific
blood parameters representative of a user's condition. The sensor
12 monitors glucose levels in the body, and may be used in
conjunction with automated or semi-automated medication infusion
pumps of the external or implantable type as described in U.S. Pat.
No. 4,562,751; 4,678,408; 4,685,903 or 4,573,994, to control
delivery of insulin to a diabetic patient.
[0041] Particular embodiments of the flexible electrochemical
sensor 12 are constructed in accordance with thin film mask
techniques to include elongated thin film conductors embedded or
encased between layers of a selected insulative material such as
polyimide film or sheet, and membranes. The sensor electrodes 20 at
a tip end of the sensing portion 18 are exposed through one of the
insulative layers for direct contact with patient blood or other
body fluids, when the sensing portion 18 (or active portion) of the
sensor 12 is subcutaneously placed at an insertion site. The
sensing portion 18 is joined to a connection portion 24 that
terminates in conductive contact pads, or the like, which are also
exposed through one of the insulative layers. In alternative
embodiments, other types of implantable sensors, such as chemical
based, optical based, or the like, may be used.
[0042] As is known in the art, the connection portion 24 and the
contact pads are generally adapted for a direct wired electrical
connection to a suitable monitor or sensor electronics device 100
for monitoring a user's condition in response to signals derived
from the sensor electrodes 20. Further description of flexible thin
film sensors of this general type are be found in U.S. Pat. No.
5,391,250, entitled METHOD OF FABRICATING THIN FILM SENSORS, which
is herein incorporated by reference. The connection portion 24 may
be conveniently connected electrically to the monitor or sensor
electronics device 100 or by a connector block 28 (or the like) as
shown and described in U.S. Pat. No. 5,482,473, entitled FLEX
CIRCUIT CONNECTOR, which is also herein incorporated by reference.
Thus, in accordance with embodiments of the present invention,
subcutaneous sensor sets 10 may be configured or formed to work
with either a wired or a wireless characteristic monitor
system.
[0043] The sensor electrodes 10 may be used in a variety of sensing
applications and may be configured in a variety of ways. For
example, the sensor electrodes 10 may be used in physiological
parameter sensing applications in which some type of biomolecule is
used as a catalytic agent. For example, the sensor electrodes 10
may be used in a glucose and oxygen sensor having a glucose oxidase
enzyme catalyzing a reaction with the sensor electrodes 20. The
sensor electrodes 10, along with a biomolecule or some other
catalytic agent, may be placed in a human body in a vascular or
non-vascular environment. For example, the sensor electrodes 20 and
biomolecule may be placed in a vein and be subjected to a blood
stream, or may be placed in a subcutaneous or peritoneal region of
the human body.
[0044] The monitor 100 may also be referred to as a sensor
electronics device 100. The monitor 100 may include a power source
110, a sensor interface 122, processing electronics 124, and data
formatting electronics 128. The monitor 100 may be coupled to the
sensor set 10 by a cable 102 through a connector that is
electrically coupled to the connector block 28 of the connection
portion 24. In an alternative embodiment, the cable may be omitted.
In this embodiment of the invention, the monitor 100 may include an
appropriate connector for direct connection to the connection
portion 104 of the sensor set 10. The sensor set 10 may be modified
to have the connector portion 104 positioned at a different
location, e.g., on top of the sensor set to facilitate placement of
the monitor 100 over the sensor set.
[0045] In embodiments of the invention, the sensor interface 122,
the processing electronics 124, and the data formatting electronics
128 are formed as separate semiconductor chips, however alternative
embodiments may combine the various semiconductor chips into a
single or multiple customized semiconductor chips. The sensor
interface 122 connects with the cable 102 that is connected with
the sensor set 10.
[0046] The power source 110 may be a battery. The battery can
include three series silver oxide 357 battery cells. In alternative
embodiments, different battery chemistries may be utilized, such as
lithium based chemistries, alkaline batteries, nickel metalhydride,
or the like, and different number of batteries may used. The
monitor 100 provides power, through the power source 110, provides
power, through the cable 102 and cable connector 104 to the sensor
set. In an embodiment of the invention, the power is a voltage
provided to the sensor set 10. In an embodiment of the invention,
the power is a current provided to the sensor set 10. In an
embodiment of the invention, the power is a voltage provided at a
specific voltage to the sensor set 10.
[0047] FIGS. 2A and 2B illustrate an implantable sensor and
electronics for driving the implantable sensor according to an
embodiment of the present invention. FIG. 2A shows a substrate 220
having two sides, a first side 222 of which contains an electrode
configuration and a second side 224 of which contains electronic
circuitry. As may be seen in FIG. 2A, a first side 222 of the
substrate comprises two counter electrode-working electrode pairs
240, 242, 244, 246 on opposite sides of a reference electrode 248.
A second side 224 of the substrate comprises electronic circuitry.
As shown, the electronic circuitry may be enclosed in a
hermetically sealed casing 226, providing a protective housing for
the electronic circuitry. This allows the sensor substrate 220 to
be inserted into a vascular environment or other environment which
may subject the electronic circuitry to fluids. By sealing the
electronic circuitry in a hermetically sealed casing 226, the
electronic circuitry may operate without risk of short circuiting
by the surrounding fluids. Also shown in FIG. 2A are pads 228 to
which the input and output lines of the electronic circuitry may be
connected. The electronic circuitry itself may be fabricated in a
variety of ways. According to an embodiment of the present
invention, the electronic circuitry may be fabricated as an
integrated circuit using techniques common in the industry.
[0048] FIG. 2B illustrates a general block diagram of an electronic
circuit for sensing an output of a sensor according to an
embodiment of the present invention. At least one pair of sensor
electrodes 310 may interface to a data converter 312, the output of
which may interface to a counter 314. The counter 314 may be
controlled by control logic 316. The output of the counter 314 may
connect to a line interface 318. The line interface 318 may be
connected to input and output lines 320 and may also connect to the
control logic 316. The input and output lines 320 may also be
connected to a power rectifier 322.
[0049] The sensor electrodes 310 may be used in a variety of
sensing applications and may be configured in a variety of ways.
For example, the sensor electrodes 310 may be used in physiological
parameter sensing applications in which some type of biomolecule is
used as a catalytic agent. For example, the sensor electrodes 310
may be used in a glucose and oxygen sensor having a glucose oxidase
enzyme catalyzing a reaction with the sensor electrodes 310. The
sensor electrodes 310, along with a biomolecule or some other
catalytic agent, may be placed in a human body in a vascular or
non-vascular environment. For example, the sensor electrodes 310
and biomolecule may be placed in a vein and be subjected to a blood
stream.
[0050] FIG. 3 illustrates a block diagram of a sensor electronics
device and a sensor including a plurality of electrodes according
to an embodiment of the invention. The sensor set or system 350
includes a sensor 355 and a sensor electronics device 360. The
sensor 355 includes a counter electrode 365, a reference electrode
370, and a working electrode 375. The sensor electronics device 360
includes a power supply 380, a regulator 385, a signal processor
390, a measurement processor 395, and a display/transmission module
397. The power supply 380 provides power (in the form of either a
voltage, a current, or a voltage including a current) to the
regulator 385. The regulator 385 transmits a regulated voltage to
the sensor 355. In an embodiment of the invention, the regulator
385 transmits a voltage to the counter electrode 365 of the sensor
355.
[0051] The sensor 355 creates a sensor signal indicative of a
concentration of a physiological characteristic being measured. For
example, the sensor signal may be indicative of a blood glucose
reading. In an embodiment of the invention utilizing subcutaneous
sensors, the sensor signal may represent a level of hydrogen
peroxide in a subject. In an embodiment of the invention where
blood or cranial sensors are utilized, the amount of oxygen is
being measured by the sensor and is represented by the sensor
signal. In an embodiment of the invention utilizing implantable or
long-term sensors, the sensor signal may represent a level of
oxygen in the subject. The sensor signal is measured at the working
electrode 375. In an embodiment of the invention, the sensor signal
may be a current measured at the working electrode. In an
embodiment of the invention, the sensor signal may be a voltage
measured at the working electrode.
[0052] The signal processor 390 receives the sensor signal (e.g., a
measured current or voltage) after the sensor signal is measured at
the sensor 355 (e.g., the working electrode). The signal processor
390 processes the sensor signal and generates a processed sensor
signal. The measurement processor 395 receives the processed sensor
signal and calibrates the processed sensor signal utilizing
reference values. In an embodiment of the invention, the reference
values are stored in a reference memory and provided to the
measurement processor 395. The measurement processor 395 generates
sensor measurements. The sensor measurements may be stored in a
measurement memory (not pictured). The sensor measurements may be
sent to a display/transmission device to be either displayed on a
display in a housing with the sensor electronics or to be
transmitted to an external device.
[0053] The sensor electronics device 360 may be a monitor which
includes a display to display physiological characteristics
readings. The sensor electronics device 360 may also be installed
in a desktop computer, a pager, a television including
communications capabilities, a laptop computer, a server, a network
computer, a personal digital assistant (PDA), a portable telephone
including computer functions, an infusion pump including a display,
a glucose sensor including a display, and or a combination infusion
pump/glucose sensor. The sensor electronics device 360 may be
housed in a blackberry, a network device, a home network device, or
an appliance connected to a home network.
[0054] FIG. 4 illustrates an alternative embodiment of the
invention including a sensor and a sensor electronics device
according to an embodiment of the present invention. The sensor set
or sensor system 400 includes a sensor electronics device 360 and a
sensor 355. The sensor includes a counter electrode 365, a
reference electrode 370, and a working electrode 375. The sensor
electronics device 360 includes a microcontroller 410 and a
digital-to-analog converter (DAC) 420. The sensor electronics
device 360 may also include a current-to-frequency converter (I/F
converter) 430.
[0055] The microcontroller 410 includes software program code,
which when executed, or programmable logic which, causes the
microcontroller 410 to transmit a signal to the DAC 420, where the
signal is representative of a voltage level or value that is to be
applied to the sensor 355. The DAC 420 receives the signal and
generates the voltage value at the level instructed by the
microcontroller 410. In embodiments of the invention, the
microcontroller 410 may change the representation of the voltage
level in the signal frequently or infrequently. Illustratively, the
signal from the microcontroller 410 may instruct the DAC 420 to
apply a first voltage value for one second and a second voltage
value for two seconds.
[0056] The sensor 355 may receive the voltage level or value. In an
embodiment of the invention, the counter electrode 365 may receive
the output of an operational amplifier which has as inputs the
reference voltage and the voltage value from the DAC 420. The
application of the voltage level causes the sensor 355 to create a
sensor signal indicative of a concentration of a physiological
characteristic being measured. In an embodiment of the invention,
the microcontroller 410 may measure the sensor signal (e.g., a
current value) from the working electrode. Illustratively, a sensor
signal measurement circuit 431 may measure the sensor signal. In an
embodiment of the invention, the sensor signal measurement circuit
431 may include a resistor and the current may be passed through
the resistor to measure the value of the sensor signal. In an
embodiment of the invention, the sensor signal may be a current
level signal and the sensor signal measurement circuit 431 may be a
current-to-frequency (I/F) converter 430. The current-to-frequency
converter 430 may measure the sensor signal in terms of a current
reading, convert it to a frequency-based sensor signal, and
transmit the frequency-based sensor signal to the microcontroller
410. In embodiments of the invention, the microcontroller 410 may
be able to receive frequency-based sensor signals easier than
non-frequency-based sensor signals. The microcontroller 410
receives the sensor signal, whether frequency-based or non
frequency-based, and determines a value for the physiological
characteristic of a subject, such as a blood glucose level. The
microcontroller 410 may include program code, which when executed
or run, is able to receive the sensor signal and convert the sensor
signal to a physiological characteristic value. In an embodiment of
the invention, the microcontroller 410 may convert the sensor
signal to a blood glucose level. In an embodiment of the invention,
the microcontroller 410 may utilize measurements stored within an
internal memory in order to determine the blood glucose level of
the subject. In an embodiment of the invention, the microcontroller
410 may utilize measurements stored within a memory external to the
microcontroller 410 to assist in determining the blood glucose
level of the subject.
[0057] After the physiological characteristic value is determined
by the microcontroller 410, the microcontroller 410 may store
measurements of the physiological characteristic values for a
number of time periods. For example, a blood glucose value may be
sent to the microcontroller 410 from the sensor every second or
five seconds, and the microcontroller may save sensor measurements
for five minutes or ten minutes of BG readings. The microcontroller
410 may transfer the measurements of the physiological
characteristic values to a display on the sensor electronics device
450. For example, the sensor electronics device 450 may be a
monitor which includes a display that provides a blood glucose
reading for a subject. In an embodiment of the invention, the
microcontroller 410 may transfer the measurements of the
physiological characteristic values to an output interface of the
microcontroller 410. The output interface of the microcontroller
410 may transfer the measurements of the physiological
characteristic values, e.g., blood glucose values, to an external
device, e.g., such as an infusion pump, a combined infusion
pump/glucose meter, a computer, a personal digital assistant, a
pager, a network appliance, a server, a cellular phone, or any
computing device.
[0058] FIG. 5 illustrates an electronic block diagram of the sensor
electrodes and a voltage being applied to the sensor electrodes
according to an embodiment of the present invention. In the
embodiment of the invention illustrated in FIG. 5, an op amp 530 or
other servo controlled device may connect to sensor electrodes 510
through a circuit/electrode interface 538. The op amp 530,
utilizing feedback through the sensor electrodes, attempts to
maintain a prescribed voltage (what the DAC may desire the applied
voltage to be) between a reference electrode 532 and a working
electrode 534 by adjusting the voltage at a counter electrode 536.
Current may then flow from a counter electrode 536 to a working
electrode 534. Such current may be measured to ascertain the
electrochemical reaction between the sensor electrodes 510 and the
biomolecule of a sensor that has been placed in the vicinity of the
sensor electrodes 510 and used as a catalyzing agent. The circuitry
disclosed in FIG. 5 may be utilized in a long-term or implantable
sensor or may be utilized in a short-teim or subcutaneous
sensor.
[0059] In a long-term sensor embodiment, where a glucose oxidase
enzyme is used as a catalytic agent in a sensor, current may flow
from the counter electrode 536 to a working electrode 534 only if
there is oxygen in the vicinity of the enzyme and the sensor
electrodes 10. Illustratively, if the voltage set at the reference
electrode 532 is maintained at about 0.5 volts, the amount of
current flowing from a counter electrode 536 to a working electrode
534 has a fairly linear relationship with unity slope to the amount
of oxygen present in the area surrounding the enzyme and the
electrodes. Thus, increased accuracy in determining an amount of
oxygen in the blood may be achieved by maintaining the reference
electrode 532 at about 0.5 volts and utilizing this region of the
current-voltage curve for varying levels of blood oxygen. Different
embodiments of the present invention may utilize different sensors
having biomolecules other than a glucose oxidase enzyme and may,
therefore, have voltages other than 0.5 volts set at the reference
electrode.
[0060] As discussed above, during initial implantation or insertion
of the sensor 510, a sensor 510 may provide inaccurate readings due
to the adjusting of the subject to the sensor and also
electrochemical byproducts caused by the catalyst utilized in the
sensor. A stabilization period is needed for many sensors in order
for the sensor 510 to provide accurate readings of the
physiological parameter of the subject. During the stabilization
period, the sensor 510 does not provide accurate blood glucose
measurements. Users and manufacturers of the sensors may desire to
improve the stabilization timeframe for the sensor so that the
sensors can be utilized quickly after insertion into the subject's
body or a subcutaneous layer of the subject.
[0061] In previous sensor electrode systems, the stabilization
period or timeframe was one hour to three hours. In order to
decrease the stabilization period or timeframe and increase the
timeliness of accuracy of the sensor, a sensor (or electrodes of a
sensor) may be subjected to a number of pulses rather than the
application of one pulse followed by the application of another
voltage. FIG. 6A illustrates a method of applying pulses during
stabilization timeframe in order to reduce the stabilization
timeframe according to an embodiment of the present invention. In
this embodiment of the invention, a voltage application device
applies 600 a first voltage to an electrode for a first time or
time period. In an embodiment of the invention, the first voltage
may be a DC constant voltage. This results in an anodic current
being generated. In an alternative embodiment of the invention, a
digital-to-analog converter or another voltage source may supply
the voltage to the electrode for a first time period. The anodic
current means that electrons are being driven away from electrode
to which the voltage is applied. In an embodiment of the invention,
an application device may apply a current instead of a voltage. In
an embodiment of the invention where a voltage is applied to a
sensor, after the application of the first voltage to the
electrode, the voltage regulator may not apply 605 a voltage for a
second time, timeframe, or time period. In other words, the voltage
application device waits until a second time period elapses. The
non-application of voltage results in a cathodic current, which
results in the gaining of electrons by the electrode to which the
voltage is not applied. The application of the first voltage to the
electrode for a first time period followed by the non-application
of voltage for a second time period is repeated 610 for a number of
iterations. This may be referred to as an anodic and cathodic
cycle. In an embodiment of the invention, the number of total
iterations of the stabilization method is three, i.e., three
applications of the voltage for the first time period, each
followed by no application of the voltage three times for the
second time period. In an embodiment of the invention, the first
voltage may be 1.07 volts. In an embodiment of the invention, the
first voltage may be 0.535 volts. In an embodiment of the
invention, the first voltage may be approximately 0.7 volts.
[0062] The result of the repeated application of the voltage and
the non-application of the voltage results in the sensor (and thus
the electrodes) being subjected to an anodic-cathodic cycle. The
anodic-cathodic cycle results in the reduction of electrochemical
byproducts which are generated by a patient's body reacting to the
insertion of the sensor or the implanting of the sensor. In an
embodiment of the invention, the electrochemical byproducts cause
generation of a background current, which results in inaccurate
measurements of the physiological parameter of the subject. In an
embodiment of the invention, the electrochemical byproduct may be
eliminated. Under other operating conditions, the electrochemical
byproducts may be reduced or significantly reduced. A successful
stabilization method results in the anodic-cathodic cycle reaching
equilibrium, electrochemical byproducts being significantly
reduced, and background current being minimized.
[0063] In an embodiment of the invention, the first voltage being
applied to the electrode of the sensor may be a positive voltage.
In an embodiment of the invention, the first voltage being applied
may be a negative voltage. In an embodiment of the invention, the
first voltage may be applied to a working electrode. In an
embodiment of the invention, the first voltage may be applied to
the counter electrode or the reference electrode.
[0064] In embodiments of the invention, the duration of the voltage
pulse and the no application of voltage may be equal, e.g., such as
three minutes each. In embodiments of the invention, the duration
of the voltage application or voltage pulse may be different
values, e.g., the first time and the second time may be different.
In an embodiment of the invention, the first time period may be
five minutes and the waiting period may be two minutes. In an
embodiment of the invention, the first time period may be two
minutes and the waiting period (or second timeframe) may be five
minutes. In other words, the duration for the application of the
first voltage may be two minutes and there may be no voltage
applied for five minutes. This timeframe is only meant to be
illustrative and should not be limiting. For example, a first
timeframe may be two, three, five or ten minutes and the second
timeframe may be five minutes, ten minutes, twenty minutes, or the
like. The timeframes (e.g., the first time and the second time) may
depend on unique characteristics of different electrodes, the
sensors, and/or the patient's physiological characteristics.
[0065] In embodiments of the invention, more or less than three
pulses may be utilized to stabilize the glucose sensor. In other
words, the number of iterations may be greater than 3 or less than
three. For example, four voltage pulses (e.g., a high voltage
followed by no voltage) may be applied to one of the electrodes or
six voltage pulses may be applied to one of the electrodes.
[0066] Illustratively, three consecutive pulses of 1.07 volts
(followed by three pulses of no volts) may be sufficient for a
sensor implanted subcutaneously. In an embodiment of the invention,
three consecutive voltage pulses of 0.7 volts may be utilized. The
three consecutive pulses may have a higher or lower voltage value,
either negative or positive, for a sensor implanted in blood or
cranial fluid, e.g., the long-term or permanent sensors. In
addition, more than three pulses (e.g., five, eight, twelve) may be
utilized to create the anodic-cathodic cycling between anodic and
cathodic currents in any of the subcutaneous, blood, or cranial
fluid sensors.
[0067] FIG. 6B illustrates a method of stabilizing sensors
according to an embodiment of the present invention. In the
embodiment of the invention illustrated in FIG. 6B, a voltage
application device may apply 630 a first voltage to the sensor for
a first time to initiate an anodic cycle at an electrode of the
sensor. The voltage application device may be a DC power supply, a
digital-to-analog converter, or a voltage regulator. After the
first time period has elapsed, a second voltage is applied 635 to
the sensor for a second time to initiate an cathodic cycle at an
electrode of the sensor. Illustratively, rather than no voltage
being applied, as is illustrated in the method of FIG. 6A, a
different voltage (from the first voltage) is applied to the sensor
during the second timeframe. In an embodiment of the invention, the
application of the first voltage for the first time and the
application of the second voltage for the second time are applied
640 for a number of iterations. In an embodiment of the invention,
the application of the first voltage for the first time and the
application of the second voltage for the second time may each be
applied for a stabilization timeframe, e.g., 10 minutes, 15
minutes, or 20 minutes rather than for a number of iterations. This
stabilization timeframe is the entire timeframe for the
stabilization sequence, e.g., until the sensor (and electrodes) are
stabilized. The benefit of this stabilization methodology is a
faster run-in of the sensors, less background current (in other
words a suppression of some the background current), and a better
glucose response.
[0068] In an embodiment of the invention, the first voltage may be
0.535 volts applied for five minutes, the second voltage may be
1.070 volts applied for two minutes, the first voltage of 0.535
volts may be applied for five minutes, the second voltage of 1.070
volts may be applied for two minutes, the first voltage of 0.535
volts may be applied for five minutes, and the second voltage of
1.070 volts may be applied for two minutes. In other words, in this
embodiment, there are three iterations of the voltage pulsing
scheme. The pulsing methodology may be changed in that the second
timeframe, e.g., the timeframe of the application of the second
voltage may be lengthened from two minutes to five minutes, ten
minutes, fifteen minutes, or twenty minutes. In addition, after the
three iterations are applied in this embodiment of the invention, a
nominal working voltage of 0.535 volts may be applied.
[0069] The 1.08 and 0.535 volts are illustrative values. Other
voltage values may be selected based on a variety of factors. These
factors may include the type of enzyme utilized in the sensor, the
membranes utilized in the sensor, the operating period of the
sensor, the length of the pulse, and/or the magnitude of the pulse.
Under certain operating conditions, the first voltage may be in a
range of 1.00 to 1.09 volts and the second voltage may be in a
range of 0.510 to 0.565 volts. In other operating embodiments, the
ranges that bracket the first voltage and the second voltage may
have a higher range, e.g., 0.3 volts, 0.6 volts, 0.9 volts,
depending on the voltage sensitivity of the electrode in the
sensor. Under other operating conditions, the voltage may be in a
range of 0.8 volts to 1.34 volts and the other voltage may be in a
range of 0.335 to 0.735. Under other operating conditions, the
range of the higher voltage may be smaller than the range of the
lower voltage. Illustratively, the higher voltage may be in a range
of 0.9 to 1.09 volts and the lower voltage may be in a range of
0.235 to 0.835.
[0070] In an embodiment of the invention, the first voltage and the
second voltage may be positive voltages, or alternatively in other
embodiments of the invention, negative voltages. In an embodiment
of the invention, the first voltage may be positive and the second
voltage may be negative, or alternatively, the first voltage may be
negative and the second voltage may be positive. The first voltage
may be different voltage levels for each of the iterations. In an
embodiment of the invention, the first voltage may be a D.C.
constant voltage. In other embodiments of the invention, the first
voltage may be a ramp voltage, a sinusoid-shaped voltage, a stepped
voltage, or other commonly utilized voltage waveforms. In an
embodiment of the invention, the second voltage may be a D.C.
constant voltage, a ramp voltage, a sinusoid-shaped voltage, a
stepped voltage, or other commonly utilized voltage waveforms. In
an embodiment of the invention, the first voltage or the second
voltage may be an AC signal riding on a DC waveform. In an
embodiment of the invention, the first voltage may be one type of
voltage, e.g., a ramp voltage, and the second voltage may be a
second type of voltage, e.g., a sinusoid-shaped voltage. In an
embodiment of the invention, the first voltage (or the second
voltage) may have different waveform shapes for each of the
iterations. For example, if there are three cycles in a
stabilization method, in a first cycle, the first voltage may be a
ramp voltage, in the second cycle, the first voltage may be a
constant voltage, and in the third cycle, the first voltage may be
a sinusoidal voltage.
[0071] In an embodiment of the invention, a duration of the first
timeframe and a duration of the second timeframe may have the same
value, or alternatively, the duration of the first timeframe and
the second timeframe may have different values. For example, the
duration of the first timeframe may be two minutes and the duration
of the second timeframe may be five minutes and the number of
iterations may be three. As discussed above, the stabilization
method may include a number of iterations. In embodiments of the
invention, during different iterations of the stabilization method,
the duration of each of the first timeframes may change and the
duration of each of the second timeframes may change.
Illustratively, during the first iteration of the anodic-cathodic
cycling, the first timeframe may be 2 minutes and the second
timeframe may be 5 minutes. During the second iteration, the first
timeframe may be 1 minute and the second timeframe may be 3
minutes. During the third iteration, the first timeframe may be 3
minutes and the second timeframe may be 10 minutes.
[0072] In an embodiment of the invention, a first voltage of 0.535
volts is applied to an electrode in a sensor for two minutes to
initiate an anodic cycle, then a second voltage of 1.07 volts is
applied to the electrode to the sensor for five minutes to initiate
a cathodic cycle. The first voltage of 0.535 volts is then applied
again for two minutes to initiate the anodic cycle and a second
voltage of 1.07 volts is applied to the sensor for five minutes. In
a third iteration, 0.535 volts is applied for two minutes to
initiate the anodic cycle and then 1.07 volts is applied for five
minutes. The voltage applied to the sensor is then 0.535 during the
actual working timeframe of the sensor, e.g., when the sensor
provides readings of a physiological characteristic of a
subject.
[0073] Shorter duration voltage pulses may be utilized in the
embodiment of FIGS. 6A and 6B. The shorter duration voltage pulses
may be utilized to apply the first voltage, the second voltage, or
both. In an embodiment of the present invention, the magnitude of
the shorter duration voltage pulse for the first voltage is -1.07
volts and the magnitude of the shorter duration voltage pulse for
the second voltage is approximately half of the high magnitude,
e.g., -0.535 volts. Alternatively, the magnitude of the shorter
duration pulse for the first voltage may be 0.535 volts and the
magnitude of the shorter duration pulse for the second voltage is
1.07 volts.
[0074] In embodiments of the invention utilizing short duration
pulses, the voltage may not be applied continuously for the entire
first time period. Instead, in the first time period, the voltage
application device may transmit a number of short duration pulses
during the first time period. In other words, a number of
mini-width or short duration voltage pulses may be applied to the
electrodes of the sensors over the first time period. Each
mini-width or short duration pulse may a width of a number of
milliseconds. Illustratively, this pulse width may be 30
milliseconds, 50 milliseconds, 70 milliseconds or 200 milliseconds.
These values are meant to be illustrative and not limiting. In an
embodiment of the invention, such as the embodiment illustrated in
FIG. 6A, these short duration pulses are applied to the sensor
(electrode) for the first time period and then no voltage is
applied for the second time period.
[0075] In an embodiment of the invention, each short duration pulse
may have the same time duration within the first time period. For
example, each short duration voltage pulse may have a time width of
50 milliseconds and each pulse delay between the pulses may be 950
milliseconds. In this example, if two minutes is the measured time
for the first timeframe, then 120 short duration voltage pulses may
be applied to the sensor. In an embodiment of the invention, each
of the short duration voltage pulses may have different time
durations. In an embodiment of the invention, each of the short
duration voltage pulses may have the same amplitude values. In an
embodiment of the invention, each of the short duration voltage
pulses may have different amplitude values. By utilizing short
duration voltage pulses rather than a continuous application of
voltage to the sensors, the same anodic and cathodic cycling may
occur and the sensor (e.g., electrodes) is subjected to less total
energy or charge over time. The use of short duration voltage
pulses utilizes less power as compared to the application of
continuous voltage to the electrodes because there is less energy
applied to the sensors (and thus the electrodes).
[0076] FIG. 6C illustrates utilization of feedback in stabilizing
the sensors according to an embodiment of the present invention.
The sensor system may include a feedback mechanism to determine if
additional pulses are needed to stabilize a sensor. In an
embodiment of the invention, a sensor signal generated by an
electrode (e.g., a working electrode) may be analyzed to determine
is the sensor signal is stabilized. A first voltage is applied 630
to an electrode for a first timeframe to initiate an anodic cycle.
A second voltage is applied 635 to an electrode for a second
timeframe to initiate a cathodic cycle. In an embodiment of the
invention, an analyzation module may analyze a sensor signal (e.g.,
the current emitted by the sensor signal, a resistance at a
specific point in the sensor, an impedance at a specific node in
the sensor) and determine if a threshold measurement has been
reached 637 (e.g., determining if the sensor is providing accurate
readings by comparing against the threshold measurement). If the
sensor readings are determined to be accurate, which represents
that the electrode (and thus the sensor) is stabilized 642, no
additional application of the first voltage and/or the second
voltage may be generated. If the stability was not achieved, in an
embodiment of the invention, then an additional anodic/cathodic
cycle is initiated by the application 630 of a first voltage to an
electrode for a first time period and then the application 635 of
the second voltage to the electrode for a second time period.
[0077] In embodiments of the invention, the analyzation module may
be employed after an anodic/cathodic cycle of three applications of
the first voltage and the second voltage to an electrode of the
sensor. In an embodiment of the invention, an analyzation module
may be employed after one application of the first voltage and the
second voltage, as is illustrated in FIG. 6C.
[0078] In an embodiment of the invention, the analyzation module
may be utilized to measure a voltage emitted after a current has
been introduced across an electrode or across two electrodes. The
analyzation module may monitor a voltage level at the electrode or
at the receiving level. In an embodiment of the invention, if the
voltage level is above a certain threshold, this may mean that the
sensor is stabilized. In an embodiment of the invention, if the
voltage level falls below a threshold level, this may indicate that
the sensor is stabilized and ready to provide readings. In an
embodiment of the invention, a current may be introduced to an
electrode or across a couple of electrodes. The analyzation module
may monitor a current level emitted from the electrode. In this
embodiment of the invention, the analyzation module may be able to
monitor the current if the current is different by an order of
magnitude from the sensor signal current. If the current is above
or below a current threshold, this may signify that the sensor is
stabilized.
[0079] In an embodiment of the invention, the analyzation module
may measure an impedance between two electrodes of the sensor. The
analyzation module may compare the impedance against a threshold or
target impedance value and if the measured impedance is lower than
the target or threshold impedance, the sensor (and hence the sensor
signal) may be stabilized. In an embodiment of the invention, the
analyzation module may measure a resistance between two electrodes
of the sensor. In this embodiment of the invention, if the
analyzation module compares the resistance against a threshold or
target resistance value and the measured resistance value is less
than the threshold or target resistance value, then the analyzation
module may determine that the sensor is stabilized and that the
sensor signal may be utilized.
[0080] FIG. 7 illustrates an effect of stabilizing a sensor
according to an embodiment of the invention. Line 705 represents
blood glucose sensor readings for a glucose sensor where a previous
single pulse stabilization method was utilized. Line 710 represents
blood glucose readings for a glucose sensor where three voltage
pulses are applied (e.g., 3 voltage pulses having a duration of 2
minutes each followed by 5 minutes of no voltage being applied).
The x-axis 715 represents an amount of time. The dots 720 725 730
and 735 represent measured glucose readings, taken utilizing a
fingerstick and then input into a glucose meter. As illustrated by
the graph, the previous single pulse stabilization method took
approximately 1 hour and 30 minutes in order to stabilize to the
desired glucose reading, e.g., 100 units. In contrast, the three
pulse stabilization method took only approximately 15 minutes to
stabilize the glucose sensor and results in a drastically improved
stabilization timeframe.
[0081] FIG. 8A illustrates a block diagram of a sensor electronics
device and a sensor including a voltage generation device according
to an embodiment of the invention. The voltage generation or
application device 810 includes electronics, logic, or circuits
which generate voltage pulses. The sensor electronics device 360
may also include an input device 820 to receive reference values
and other useful data. In an embodiment of the invention, the
sensor electronics device may include a measurement memory 830 to
store sensor measurements. In this embodiment of the invention, the
power supply 380 may supply power to the sensor electronics device.
The power supply 380 may supply power to a regulator 385, which
supplies a regulated voltage to the voltage generation or
application device 810. The connection terminals 811 represent that
in the illustrated embodiment of the invention, the connection
terminal couples or connects the sensor 355 to the sensor
electronics device 360.
[0082] In an embodiment of the invention illustrated in FIG. 8A,
the voltage generation or application device 810 supplies a
voltage, e.g., the first voltage or the second voltage, to an input
terminal of an operational amplifier 840. The voltage generation or
application device 810 may also supply the voltage to a working
electrode 375 of the sensor 355. Another input terminal of the
operational amplifier 840 is coupled to the reference electrode 370
of the sensor. The application of the voltage from the voltage
generation or application device 810 to the operational amplifier
840 drives a voltage measured at the counter electrode 365 to be
close to or equal the voltage applied at the working electrode 375.
In an embodiment of the invention, the voltage generation or
application device 810 could be utilized to apply the desired
voltage between the counter electrode and the working electrode.
This may occur by the application of the fixed voltage to the
counter electrode directly.
[0083] In an embodiment of the invention as illustrated in FIGS. 6A
and 6B, the voltage generation device 810 generates a first voltage
that is to be applied to the sensor during a first timeframe. The
voltage generation device 810 transmits this first voltage to an op
amp 840 which drives the voltage at a counter electrode 365 of the
sensor 355 to the first voltage. In an embodiment of the invention,
the voltage generation device 810 also could transmit the first
voltage directly to the counter electrode 365 of the sensor 355. In
the embodiment of the invention illustrated in FIG. 6A, the voltage
generation device 810 then does not transmit the first voltage to
the sensor 355 for a second timeframe. In other words, the voltage
generation device 810 is turned off or switched off. The voltage
generation device 810 may be programmed to continue cycling between
applying the first voltage and not applying a voltage for either a
number of iterations or for a stabilization timeframe, e.g., for
twenty minutes. FIG. 8B illustrates a voltage generation device to
implement this embodiment of the invention. The voltage regulator
385 transfers the regulated voltage to the voltage generation
device 810. A control circuit 860 controls the closing and opening
of a switch 850. If the switch 850 is closed, the voltage is
applied. If the switch 850 is opened, the voltage is not applied.
The timer 865 provides a signal to the control circuit 860 to
instruct the control circuit 860 to turn on and off the switch 850.
The control circuit 860 includes logic which can instruct the
circuit to open and close the switch 850 a number of times (to
match the necessary iterations). In an embodiment of the invention,
the timer 865 may also transmit a stabilization signal to identify
that the stabilization sequence is completed, i.e. that a
stabilization timeframe has elapsed.
[0084] In an embodiment of the invention, the voltage generation
device generates a first voltage for a first timeframe and
generates a second voltage for a second timeframe. FIG. 8C
illustrates a voltage generation device to generate two voltage
values according in a sensor electronics device according to
implement this embodiment of the invention. In this embodiment of
the invention, a two position switch 870 is utilized.
Illustratively, if the first switch position 871 is turned on or
closed by the timer 865 instructing the control circuit 860, then
the voltage generation device 810 generates a first voltage for the
first timeframe. After the first voltage has been applied for the
first timeframe, timer sends a signal to the control circuit 860
indicating the first timeframe has elapsed and the control circuit
860 directs the switch 870 to move to the second position 872. When
the switch 870 is at the second position 872, the regulated voltage
is directed to a voltage step-down or buck converter 880 to reduce
the regulated voltage to a lesser value. The lesser value is then
delivered to the op amp 840 for the second timeframe. After the
timer 865 has sent a signal to the control circuit 860 that the
second timeframe has elapsed, then the control circuit 860 moves
the switch 870 back to the first position. This continues until the
desired number of iterations has been completed or the
stabilization timeframe has elapsed. In an embodiment of the
invention, after the sensor stabilization timeframe has elapsed,
the sensor transmits a sensor signal 350 to the signal processor
390.
[0085] FIG. 8D illustrates a voltage application device 810
utilized to perform more complex applications of voltage to the
sensor. The voltage application device 810 may include a control
device 860, a switch 890, a sinusoid generation device 891, a ramp
voltage generation device 892, and a constant voltage generation
device 893. In other embodiments of the invention, the voltage
application may generate an AC wave on top of a DC signal or other
various voltage pulse waveforms. In the embodiment of the invention
illustrated in FIG. 8D, the control device 860 may cause the switch
to move to one of the three voltage generation systems 891
(sinusoid), 892 (ramp), 893 (constant DC). This results in each of
the voltage regulation systems generating the identified voltage
waveform. Under certain operating conditions, e.g., where a
sinusoidal pulse is to be applied for three pulses, the control
device 860 may cause the switch 890 to connect the voltage from the
voltage regulator 385 to the sinusoid voltage generator 891 in
order for the voltage application device 810 to generate a
sinusoidal voltage. Under other operating conditions, e.g., when a
ramp voltage is applied to the sensor as the first voltage for a
first pulse of three pulses, a sinusoid voltage is applied to the
sensor as the first voltage for a second pulse of the three pulses,
and a constant DC voltage is applied to the sensor as the first
voltage for a third pulse of the three pulses, the control device
860 may cause the switch 890, during the first timeframes in the
anodic/cathodic cycles, to move between connecting the voltage from
the voltage generation or application device 810 to the ramp
voltage generation system 891, then to the sinusoidal voltage
generation system 892, and then to the constant DC voltage
generation system 893. In this embodiment of the invention, the
control device 860 may also be directing or controlling the switch
to connect certain ones of the voltage generation subsystems to the
voltage from the regulator 385 during the second timeframe, e.g.,
during application of the second voltage.
[0086] FIG. 9A illustrates a sensor electronics device including a
microcontroller for generating voltage pulses according to an
embodiment of the present invention. The advanced sensor
electronics device may include a microcontroller 410 (see FIG. 4),
a digital-to-analog converter (DAC) 420, an op amp 840, and a
sensor signal measurement circuit 431. In an embodiment of the
invention, the sensor signal measurement circuit may be a
current-to-frequency (I/F) converter 430. In the embodiment of the
invention illustrated in FIG. 9A, software or programmable logic in
the microcontroller 410 provides instructions to transmit signals
to the DAC 420, which in turn instructs the DAC 420 to output a
specific voltage to the operational amplifier 840. The
microcontroller 410 may also be instructed to output a specific
voltage to the working electrode 375, as is illustrated by line 911
in FIG. 9A. As discussed above, the application of the specific
voltage to operational amplifier 840 and the working electrode 375
may drive the voltage measured at the counter electrode to the
specific voltage magnitude. In other words, the microcontroller 410
outputs a signal which is indicative of a voltage or a voltage
waveform that is to be applied to the sensor 355 (e.g., the
operational amplifier 840 coupled to the sensor 355). In an
alternative embodiment of the invention, a fixed voltage may be set
by applying a voltage directly from the DAC 420 between the
reference electrode and the working electrode 375. A similar result
may also be obtained by applying voltages to each of the electrodes
with the difference equal to the fixed voltage applied between the
reference and working electrode. In addition, the fixed voltage may
be set by applying a voltage between the reference and the counter
electrode. Under certain operating conditions, the microcontroller
410 may generates a pulse of a specific magnitude which the DAC 420
understands represents that a voltage of a specific magnitude is to
be applied to the sensor. After a first timeframe, the
microcontroller 410 (via the program or programmable logic) outputs
a second signal which either instructs the DAC 420 to output no
voltage (for a sensor electronics device 360 operating according to
the method described in FIG. 6A) or to output a second voltage (for
a sensor electronics device 360 operating according to the method
described in FIG. 6B). The microcontroller 410, after the second
timeframe has elapsed, then repeats the cycle of sending the signal
indicative of a first voltage to apply, (for the first timeframe)
and then sending the signal to instruct no voltage is to be applied
or that a second voltage is to be applied (for the second
timeframe).
[0087] Under other operating conditions, the microcontroller 410
may generate a signal to the DAC 420 which instructs the DAC to
output a ramp voltage. Under other operating conditions, the
microcontroller 410 may generate a signal to the DAC 420 which
instructs the DAC 420 to output a voltage simulating a sinusoidal
voltage. These signals could be incorporated into any of the
pulsing methodologies discussed above in the preceding paragraph or
earlier in the application. In an embodiment of the invention, the
microcontroller 410 may generate a sequence of instructions and/or
pulses, which the DAC 420 receives and understands to mean that a
certain sequence of pulses is to be applied. For example, the
microcontroller 410 may transmit a sequence of instructions (via
signals and/or pulses) that instruct the DAC 420 to generate a
constant voltage for a first iteration of a first timeframe, a ramp
voltage for a first iteration of a second timeframe, a sinusoidal
voltage for a second iteration of a first timeframe, and a
squarewave having two values for a second iteration of the second
timeframe.
[0088] The microcontroller 410 may include programmable logic or a
program to continue this cycling for a stabilization timeframe or
for a number of iterations. Illustratively, the microcontroller 410
may include counting logic to identify when the first timeframe or
the second timeframe has elapsed. Additionally, the microcontroller
410 may include counting logic to identify that a stabilization
timeframe has elapsed. After any of the preceding timeframes have
elapsed, the counting logic may instruct the microcontroller to
either send a new signal or to stop transmission of a signal to the
DAC 420.
[0089] The use of the microcontroller 410 allows a variety of
voltage magnitudes to be applied in a number of sequences for a
number of time durations. In an embodiment of the invention, the
microcontroller 410 may include control logic or a program to
instruct the digital-to-analog converter 420 to transmit a voltage
pulse having a magnitude of approximately 1.0 volt for a first time
period of 1 minute, to then transmit a voltage pulse having a
magnitude of approximately 0.5 volts for a second time period of 4
minutes, and to repeat this cycle for four iterations. In an
embodiment of the invention, the microcontroller 420 may be
programmed to transmit a signal to cause the DAC 420 to apply the
same magnitude voltage pulse for each first voltage in each of the
iterations. In an embodiment of the invention, the microcontroller
410 may be programmed to transmit a signal to cause the DAC to
apply a different magnitude voltage pulse for each first voltage in
each of the iterations. In this embodiment of the invention, the
microcontroller 410 may also be programmed to transmit a signal to
cause the DAC 420 to apply a different magnitude voltage pulse for
each second voltage in each of the iterations. Illustratively, the
microcontroller 410 may be programmed to transmit a signal to cause
the DAC 420 to apply a first voltage pulse of approximately one
volt in the first iteration, to apply a second voltage pulse of
approximately 0.5 volts in the first iteration, to apply a first
voltage of 0.7 volts and a second voltage of 0.4 volts in the
second iteration, and to apply a first voltage of 1.2 and a second
voltage of 0.8 in the third iteration.
[0090] The microcontroller 410 may also be programmed to instruct
the DAC 420 to provide a number of short duration voltage pulses
for a first timeframe. In this embodiment of the invention, rather
than one voltage being applied for the entire first timeframe
(e.g., two minutes), a number of shorter duration pulses may be
applied to the sensor. In this embodiment, the microcontroller 410
may also be programmed to program the DAC 420 to provide a number
of short duration voltage pulses for the second timeframe to the
sensor. Illustratively, the microcontroller 410 may send a signal
to cause the DAC to apply a number of short duration voltage pulses
where the short duration is 50 milliseconds or 100 milliseconds. In
between these short duration pulses the DAC may apply no voltage or
the DAC may apply a minimal voltage. The DAC 420 may cause the
microcontroller to apply the short duration voltage pulses for the
first timeframe, e.g., two minutes. The microcontroller 410 may
then send a signal to cause the DAC to either not apply any voltage
or to apply the short duration voltage pulses at a magnitude of a
second voltage for a second timeframe to the sensor, e.g., the
second voltage may be 0.75 volts and the second timeframe may be 5
minutes. In an embodiment of the invention, the microcontroller 410
may send a signal to the DAC 420 to cause the DAC 420 to apply a
different magnitude voltage for each of short duration pulses in
the first timeframe and/or in the second timeframe. In an
embodiment of the invention, the microcontroller 410 may send a
signal to the DAC 420 to cause the DAC 420 to apply a pattern of
voltage magnitudes to the short durations voltage pulses for the
first timeframe or the second timeframe. For example, the
microcontroller may transmit a signal or pulses instructing the DAC
420 to apply thirty 20 millisecond pulses to the sensor during the
first timeframe. Each of the thirty 20 millisecond pulses may have
the same magnitude or may have a different magnitude. In this
embodiment of the invention, the microcontroller 410 may instruct
the DAC 420 to apply short duration pulses during the second
timeframe or may instruct the DAC 420 to apply another voltage
waveform during the second timeframe.
[0091] Although the disclosures in FIGS. 6-8 disclose the
application of a voltage, a current may also be applied to the
sensor to initiate the stabilization process. Illustratively, in
the embodiment of the invention illustrated in FIG. 6B, a first
current may be applied during a first timeframe to initiate an
anodic or cathodic response and a second current may be applied
during a second timeframe to initiate the opposite anodic or
cathodic response. The application of the first current and the
second current may continue for a number of iterations or may
continue for a stabilization timeframe. In an embodiment of the
invention, a first current may be applied during a first timeframe
and a first voltage may be applied during a second timeframe. In
other words, one of the anodic or cathodic cycles may be triggered
by a current being applied to the sensor and the other of the
anodic or cathodic cycles may be triggered by a voltage being
applied to the sensor. As described above, a current applied may be
a constant current, a ramp current, a stepped pulse current, or a
sinusoidal current. Under certain operating conditions, the current
may be applied as a sequence of short duration pulses during the
first timeframe.
[0092] FIG. 9B illustrates a sensor and sensor electronics
utilizing an analyzation module for feedback in a stabilization
period according to an embodiment of the present invention. FIG. 9B
introduces an analyzation module 950 to the sensor electronics
device 360. The analyzation module 950 utilizes feedback from the
sensor to determine whether or not the sensor is stabilized. In an
embodiment of the invention, the microcontroller 410 may include
instructions or commands to control the DAC 420 so that the DAC 420
applies a voltage or current to a part of the sensor 355. FIG. 9B
illustrates that a voltage or current could be applied between a
reference electrode 370 and a working electrode 375. However, the
voltage or current can be applied in between electrodes or directly
to one of the electrodes and the invention should not be limited by
the embodiment illustrated in FIG. 9B. The application of the
voltage or current is illustrated by dotted line 955. The
analyzation module 950 may measure a voltage, a current, a
resistance, or an impedance in the sensor 355. FIG. 9B illustrates
that the measurement occurs at the working electrode 375, but this
should not be limit the invention because other embodiments of the
invention may measure a voltage, a current, a resistance, or an
impedance in between electrodes of the sensor or direct at either
the reference electrode 370 or the counter electrode 365. The
analyzation module 950 may receive the measured voltage, current,
resistance, or impedance and may compare the measurement to a
stored value (e.g., a threshold value). Dotted line 956 represents
the analyzation module 950 reading or taking a measurement of the
voltage, current, resistance, or impedance. Under certain operating
conditions, if the measured voltage, current, resistance, or
impedance is above the threshold, the sensor is stabilized and the
sensor signal is providing accurate readings of a physiological
condition of a patient. Under other operating conditions, if the
measured voltage, current, resistance, or impedance is below the
threshold, the sensor is stabilized. Under other operating
conditions, the analyzation module 950 may verify that the measured
voltage, current, resistance, or impedance is stable for a specific
timeframe, e.g., one minute or two minutes. This may represent that
the sensor 355 is stabilized and that the sensor signal is
transmitting accurate measurements of a subject's physiological
parameter, e.g., blood glucose level. After the analyzation module
950 has determined that the sensor is stabilized and the sensor
signal is providing accurate measurements, the analyzation module
950 may transmit a signal (e.g., a sensor stabilization signal) to
the microcontroller 410 indicating that the sensor is stabilized
and that the microcontroller 410 can start using or receiving the
sensor signal from the sensor 355. This is represented by dotted
line 957.
[0093] FIG. 10 illustrates a block diagram of a sensor system
including hydration electronics according to an embodiment of the
present invention. The sensor system includes a connector 1010, a
sensor 1012, and a monitor or sensor electronics device 1025. The
sensor 1012 includes electrodes 1020 and a connection portion 1024.
In an embodiment of the invention, the sensor 1012 may be connected
to the sensor electronics device 1025 via a connector 1010 and a
cable. In other embodiments of the invention, the sensor 1012 may
be directly connected to the sensor electronics device 1025. In
other embodiments of the invention, the sensor 1012 may be
incorporated into the same physical device as the sensor
electronics device 1025. The monitor or sensor electronics device
1025 may include a power supply 1030, a regulator 1035, a signal
processor 1040, a measurement processor 1045, and a processor 1050.
The monitor or sensor electronics device 1025 may also include a
hydration detection circuit 1060. The hydration detection circuit
1060 interfaces with the sensor 1012 to determine if the electrodes
1020 of the sensor 1012 are sufficiently hydrated. If the
electrodes 1020 are not sufficiently hydrated, the electrodes 1020
do not provide accurate glucose readings, so it is important to
know when the electrodes 1020 are sufficiently hydrated. Once the
electrodes 1020 are sufficiently hydrated, accurate glucose
readings may be obtained.
[0094] In an embodiment of the invention illustrated in FIG. 10,
the hydration detection circuit 1060 may include a delay or timer
module 1065 and a connection detection module 1070. In an
embodiment of the invention utilizing the short term sensor or the
subcutaneous sensor, after the sensor 1012 has been inserted into
the subcutaneous tissue, the sensor electronics device or monitor
1025 is connected to the sensor 1012. The connection detection
module 1070 identifies that the sensors electronics device 1025 has
been connected to the sensor 1012 and sends a signal to the timer
module 1065. This is illustrated in FIG. 10 by the arrow 1084 which
represents a detector 1083 detecting a connection and sending a
signal to the connection detection module 1070 indicating the
sensor 1012 has been connected to the sensor electronics device
1025. In an embodiment of the invention where implantable or
long-term sensors are utilized, a connection detection module 1070
identifies that the implantable sensor has been inserted into the
body. The timer module 1065 receives the connection signal and
waits a set or established hydration time. Illustratively, the
hydration time may be two minutes, five minutes, ten minutes, or 20
minutes. These examples are meant to be illustrative and not to be
limiting. The timeframe does not have to be a set number of minutes
and can include any number of seconds. In an embodiment of the
invention, after the timer module 1065 has waited for the set
hydration time, the timer module 1065 may notify the processor 1050
that the sensor 1012 is hydrated by sending a hydration signal,
which is illustrated by dotted line 1086.
[0095] In this embodiment of the invention, the processor 1050 may
receive the hydration signal and only start utilizing the sensor
signal (e.g., sensor measurements) after the hydration signal has
been received. In another embodiment of the invention, the
hydration detection circuit 1060 may be coupled between the sensor
(the sensor electrodes 1020) and the signal processor 1040. In this
embodiment of the invention, the hydration detection circuit 1060
may prevent the sensor signal from being sent to signal processor
1040 until the timer module 1065 has notified the hydration
detection circuit 1060 that the set hydration time has elapsed.
This is illustrated by the dotted lines labeled with reference
numerals 1080 and 1081. Illustratively, the timer module 1065 may
transmit a connection signal to a switch (or transistor) to turn on
the switch and let the sensor signal proceed to the signal
processor 1040. In an alternative embodiment of the invention, the
timer module 1065 may transmit a connection signal to turn on a
switch 1088 (or close the switch 1088) in the hydration detection
circuit 1060 to allow a voltage from the regulator 1035 to be
applied to the sensor 1012 after the hydration time has elapsed. In
other words, in this embodiment of the invention, the voltage from
the regulator 1035 is not applied to the sensor 1012 until after
the hydration time has elapsed.
[0096] FIG. 11 illustrates an embodiment of the invention including
a mechanical switch to assist in determining a hydration time. In
an embodiment of the invention, a single housing may include a
sensor assembly 1120 and a sensor electronics device 1125. In an
embodiment of the invention, the sensor assembly 1120 may be in one
housing and the sensor electronics device 1125 may be in a separate
housing, but the sensor assembly 1120 and the sensor electronics
device 1125 may be connected together. In this embodiment of the
invention, a connection detection mechanism 1160 may be a
mechanical switch. The mechanical switch may detect that the sensor
1120 is physically connected to the sensor electronics device 1125.
In an embodiment of the invention, a timer circuit 1135 may also be
activated when the mechanical switch 1160 detects that the sensor
1120 is connected to the sensor electronics device 1125. In other
words, the mechanical switch may close and a signal may be
transferred to a timer circuit 1135. Once a hydration time has
elapsed, the timer circuit 1135 transmits a signal to the switch
1140 to allow the regulator 1035 to apply a voltage to the sensor
1120. In other words, no voltage is applied until the hydration
time has elapsed. In an embodiment of the invention, current may
replace voltage as what is being applied to the sensor once the
hydration time elapses. In an alternative embodiment of the
invention, when the mechanical switch 1160 identifies that a sensor
1120 has been physically connected to the sensor electronics device
1125, power may initially be applied to the sensor 1120. Power
being sent to the sensor 1120 results in a sensor signal being
output from the working electrode in the sensor 1120. The sensor
signal may be measured and sent to a processor 1175. The processor
1175 may include a counter input. Under certain operating
conditions, after a set hydration time has elapsed from when the
sensor signal was input into the processor 1175, the processor 1175
may start processing the sensor signal as an accurate measurement
of the glucose in a subject's body. In other words, the processor
1175 has received the sensor signal from the potentiostat circuit
1170 for a certain amount of time, but will not process the signal
until receiving an instruction from the counter input of the
processor identifying that a hydration time has elapsed. In an
embodiment of the invention, the potentiostat circuit 1170 may
include a current-to-frequency converter 1180. In this embodiment
of the invention, the current-to-frequency converter 1180, may
receive the sensor signal as a current value and may convert the
current value into a frequency value, which is easier for the
processor 1175 to handle.
[0097] In an embodiment of the invention, the mechanical switch
1160 may also notify the processor 1175 when the sensor 1120 has
been disconnected from the sensor electronics device 1125. This is
represented by dotted line 1176 in FIG. 11. This may result in the
processor 1170 powering down or reducing power to a number of
components, chips, and/or circuits of the sensor electronics device
1125. If the sensor 1120 is not connected, the battery or power
source may be drained if the components or circuits of the sensor
electronics device 1125 are in a power on state. Accordingly, if
the mechanical switch 1160 detects that the sensor 1120 has been
disconnected from the sensor electronics device 1125, the
mechanical switch may indicate this to the processor 1175, and the
processor 1175 may power down or reduce power to one or more of the
electronic circuits, chips, or components of the sensor electronics
device 1125.
[0098] FIG. 12 illustrates an electrical method of detection of
hydration according to an embodiment of the invention. In an
embodiment of the invention, an electrical detecting mechanism for
detecting connection of a sensor may be utilized. In this
embodiment of the invention, the hydration detection electronics
1250 may include an AC source 1255 and a detection circuit 1260.
The hydration detection electronics 1250 may be located in the
sensor electronics device 1225. The sensor 1220 may include a
counter electrode 1221, a reference electrode 1222, and a working
electrode 1223. As illustrated in FIG. 12, the AC source 1255 is
coupled to a voltage setting device 1275, the reference electrode
1222, and the detection circuit 1260. In this embodiment of the
invention, an AC signal from the AC source is applied to the
reference electrode connection, as illustrated by dotted line 1291
in FIG. 12. In an embodiment of the invention, the AC signal is
coupled to the sensor 1220 through an impedance and the coupled
signal is attenuated significantly if the sensor 1220 is connected
to the sensor electronics device 1225. Thus, a low level AC signal
is present at an input to the detection circuit 1260. This may also
be referred to as a highly attenuated signal or a signal with a
high level of attenuation. Under certain operating conditions, the
voltage level of the AC signal may be
Vapplied*(Ccoupling)/(Ccoupling+Csensor). If the detection circuit
1260 detects that the a high level AC signal (lowly attenuated
signal) is present at an input terminal of the detection circuit
1260, no interrupt is sent to the microcontroller 410 because the
sensor 1220 has not been sufficiently hydrated or activated. For
example, the input of the detection circuit 1260 may be a
comparator. If the sensor 1220 is sufficiently hydrated (or
wetted), an effective capacitance forms between the counter
electrode and the reference electrode, (e.g., capacitance C.sub.r-c
in FIG. 12) and an effective capacitance forms between the
reference electrode and the working electrode (e.g., capacitance
C.sub.w-r in FIG. 12). In other words, an effective capacitance
relates to capacitance being formed between two nodes and does not
represent that an actual capacitor is placed in a circuit between
the two electrodes. In an embodiment of the invention, the AC
signal from the AC source 1255 is sufficiently attenuated by
capacitances C.sub.r-c and C.sub.w-r and the detection circuit 1260
detects the presence of a low level or highly attenuated AC signal
from the AC source 1255 at the input terminal of the detection
circuit 1260. This embodiment of the invention is significant
because the utilization of the existing connections between the
sensor 1120 and the sensor electronics device 1125 reduces the
number of connections to the sensor. In other words, the mechanical
switch, disclosed in FIG. 11, requires a switch and associated
connections between the sensor 1120 and the sensor electronics
device 1125. It is advantageous to eliminate the mechanical switch
because the sensor 1120 is continuously shrinking in size and the
elimination of components helps achieve this size reduction. In
alternative embodiments of the invention, the AC signal may be
applied to different electrodes (e.g., the counter electrode or the
working electrode) and the invention may operate in a similar
fashion.
[0099] As noted above, after the detection circuit 1260 has
detected that a low level AC signal is present at the input
terminal of the detection circuit 1260, the detection circuit 1260
may later detect that a high level AC signal, with low attenuation,
is present at the input terminal. This represents that the sensor
1220 has been disconnected from the sensor electronics device 1225
or that the sensor is not operating properly. If the sensor has
been disconnected from the sensor electronics device 1225, the AC
source may be coupled with little or low attenuation to the input
of the detection circuit 1260. As noted above, the detection
circuit 1260 may generate an interrupt to the microcontroller. This
interrupt may be received by the microcontroller and the
microcontroller may reduce or eliminate power to one or a number of
components or circuits in the sensor electronics device 1225. This
may be referred to as the second interrupt. Again, this helps
reduce power consumption of the sensor electronics device 1225,
specifically when the sensor 1220 is not connected to the sensor
electronics device 1225.
[0100] In an alternative embodiment of the election illustrated in
FIG. 12, the AC signal may be applied to the reference electrode
1222, as is illustrated by reference numeral 1291, and an impedance
measuring device 1277 may measure the impedance of an area in the
sensor 1220. Illustratively, the area may be an area between the
reference electrode and the working electrode, as illustrated by
dotted line 1292 in FIG. 12. Under certain operating conditions,
the impedance measuring device 1277 may transmit a signal to the
detection circuit 1260 if a measured impedance has decreased to
below an impedance threshold or other set criteria. This represents
that the sensor is sufficiently hydrated. Under other operating
conditions, the impedance measuring device 1277 may transmit a
signal to the detection circuit 1260 once the impedance is above an
impedance threshold. The detection circuit 1260 then transmits the
interrupt to the microcontroller 410. In another embodiment of the
invention, the detection circuit 1260 may transmit an interrupt or
signal directly to the microcontroller.
[0101] In an alternative embodiment of the invention, the AC source
1255 may be replaced by a DC source. If a DC source is utilized,
then a resistance measuring element may be utilized in place of an
impedance measuring element 1277. In an embodiment of the invention
utilizing the resistance measuring element, once the resistance
drops below a resistance threshold or a set criteria, the
resistance measuring element may transmit a signal to the detection
circuit 1260 (represented by dotted line 1293) or directly to the
microcontroller indicating that the sensor is sufficiently hydrated
and that power may be applied to the sensor.
[0102] In the embodiment of the invention illustrated in FIG. 12,
if the detection circuit 1260 detects a low level or highly
attenuated AC signal from the AC source, an interrupt is generated
to the microcontroller 410. This interrupt indicates that sensor is
sufficiently hydrated. In this embodiment of the invention, in
response to the interrupt, the microcontroller 410 generates a
signal that is transferred to a digital-to-analog converter 420 to
instruct or cause the digital-to-analog converter 420 to apply a
voltage or current to the sensor 1220. Any of the different
sequence of pulses or short duration pulses described above in FIG.
6A, 6B, or 6C or the associated text describing the application of
pulses, may be applied to the sensor 1220. Illustratively, the
voltage from the DAC 420 may be applied to an op-amp 1275, the
output of which is applied to the counter electrode 1221 of the
sensor 1220. This results in a sensor signal being generated by the
sensor, e.g., the working electrode 1223 of the sensor. Because the
sensor is sufficiently hydrated, as identified by the interrupt,
the sensor signal created at the working electrode 1223 is
accurately measuring glucose. The sensor signal is measured by a
sensor signal measuring device 431 and the sensor signal measuring
device 431 transmits the sensor signal to the microcontroller 410
where a parameter of a subject's physiological condition is
measured. The generation of the interrupt represents that a sensor
is sufficiently hydrated and that the sensor 1220 is now supplying
accurate glucose measurements. In this embodiment of the invention,
the hydration period may depend on the type and/or the manufacturer
of the sensor and on the sensor's reaction to insertion or
implantation in the subject. Illustratively, one sensor 1220 may
have a hydration time of five minutes and one sensor 1220 may have
a hydration time of one minute, two minutes, three minutes, six
minutes, or 20 minutes. Again, any amount of time may be an
acceptable amount of hydration time for the sensor, but smaller
amounts of time are preferable.
[0103] If the sensor 1220 has been connected, but is not
sufficiently hydrated or wetted, the effective capacitances
C.sub.r-c and C.sub.w-r may not attenuate the AC signal from the AC
source 1255. The electrodes in the sensor 1120 are dry before
insertion and because the electrodes are dry, a good electrical
path (or conductive path) does not exist between the two
electrodes. Accordingly, a high level AC signal or lowly attenuated
AC signal may still be detected by the detection circuit 1260 and
no interrupt may be generated. Once the sensor has been inserted,
the electrodes become immersed in the conductive body fluid. This
results in a leakage path with lower DC resistance. Also, boundary
layer capacitors form at the metal/fluid interface. In other words,
a rather large capacitance forms between the metal/fluid interface
and this large capacitance looks like two capacitors in series
between the electrodes of the sensor. This may be referred to as an
effective capacitance. In practice, a conductivity of an
electrolyte above the electrode is being measured. In some
embodiments of the invention, the glucose limiting membrane (GLM)
also illustrates impedance blocking electrical efficiency. An
unhydrated GLM results in high impedance, whereas a high moisture
GLM results in low impedance. Low impedance is desired for accurate
sensor measurements.
[0104] FIG. 13A illustrates a method of hydrating a sensor
according to an embodiment of the present invention. In an
embodiment of the invention, the sensor may be physically connected
1310 to the sensor electronics device. After the connection, in one
embodiment of the invention, a timer or counter may be initiated to
count 1320 a hydration time. After the hydration time has elapsed,
a signal may be transmitted 1330 to a subsystem in the sensor
electronics device to initiate the application of a voltage to the
sensor. As discussed above, in an embodiment of the invention, a
microcontroller may receive the signal and instruct the DAC to
apply a voltage to the sensor or in another embodiment of the
invention, a switch may receive a signal which allows a regulator
to apply a voltage to the sensor. The hydration time may be five
minutes, two minutes, ten minutes and may vary depending on the
subject and also on the type of sensor.
[0105] In an alternative embodiment of the invention, after the
connection of the sensor to the sensor electronics device, an AC
signal (e.g., a low voltage AC signal) may be applied 1340 to the
sensor, e.g., the reference electrode of the sensor. The AC signal
may be applied because the connection of the sensor to the sensor
electronics device allows the AC signal to be applied to the
sensor. After application of the AC signal, an effective
capacitance forms 1350 between the electrode in the sensor that the
voltage is applied to and the other two electrodes. A detection
circuit determines 1360 what level of the AC signal is present at
the input of the detection circuit. If a low level AC signal (or
highly attenuated AC signal) is present at the input of the
detection circuit, due to the effective capacitance fanning a good
electrical conduit between the electrodes and the resulting
attenuation of the AC signal, an interrupt is generated 1370 by the
detection circuit and sent to a microcontroller.
[0106] The microcontroller receives the interrupt generated by the
detection circuit and transmits 1380 a signal to a
digital-to-analog converter instructing or causing the
digital-to-analog converter to apply a voltage to an electrode of
the sensor, e.g., the counter electrode. The application of the
voltage to the electrode of the sensor results in the sensor
creating or generating a sensor signal 1390. A sensor signal
measurement device 431 measures the generated sensor signal and
transmits the sensor signal to the microcontroller. The
microcontroller receives 1395 the sensor signal from the sensor
signal measurement device, which is coupled to the working
electrode, and processes the sensor signal to extract a measurement
of a physiological characteristic of the subject or patient.
[0107] FIG. 13B illustrates an additional method for verifying
hydration of a sensor according to an embodiment of the present
invention. In the embodiment of the invention illustrated in FIG.
13B, the sensor is physically connected 1310 to the sensor
electronics device. In an embodiment of the invention, an AC signal
is applied 1341 to an electrode, a reference electrode, in the
sensor. Alternatively, in an embodiment of the invention, a DC
signal is applied 1341 to an electrode in the sensor. If an AC
signal is applied, an impedance measuring element measures 1351 an
impedance at a point within the sensor. Alternatively, if a DC
signal is applied a resistance measuring element measures 1351 a
resistance at a point within the sensor. If the resistance or
impedance is lower than an resistance threshold or impedance
threshold, respectively, (or other set criteria), then the
impedance (or resistance) measuring element transmits 1361 (or
allows a signal to be transmitted) to the detection circuit, and
the detection circuit transmits an interrupt identifying that the
sensor is hydrated to the microcontroller. The reference numbers
1380, 1390, and 1395 are the same in FIGS. 13A and 13B because they
represent the same action.
[0108] The microcontroller receives the interrupt and transmits
1380 a signal to a digital-to-analog converter to apply a voltage
to the sensor. In an alternative embodiment of the invention, the
digital-to-analog converter can apply a current to the sensor, as
discussed above. The sensor, e.g., the working electrode, creates
1390 a sensor signal, which represents a physiological parameter of
a patient. The microcontroller receives 1395 the sensor signal from
a sensor signal measuring device, which measures the sensor signal
at an electrode in the sensor, e.g., the working electrode. The
microcontroller processes the sensor signal to extract a
measurement of the physiological characteristic of the subject or
patient, e.g., the blood glucose level of the patient.
[0109] In still further embodiments, Open Circuit Potential (OCP)
measurements may be used to verify hydration of the sensor. In
these embodiments, OCP measurement (also known as the resting
potential) is the measurement of the potential difference between
two electrodes. In particular embodiments, the potential difference
between the reference electrode and working electrode may be
measured to determine hydration. However, in other embodiments, the
potential difference between the reference electrode and counter
electrode may be measured. In still other embodiments, the
potential difference between the working electrode and counter
electrode may be measured. In some embodiments, only one set of OCP
measurements are utilized. However, other embodiments may utilize
OCP measurements from two sets of electrodes and/or all three sets
of electrodes to determine hydration. (See FIGS. 2-5 and 8-12 for
illustrations of the working, reference and counter electrodes). In
still other embodiments, the OCP measurements are utilized in
conjunction with rate of change values obtained from the OCP values
over a specified period of time.
[0110] In use, after the open circuit potential is measured, the
hydration detection electronics compare the obtained values with
predetermined thresholds and rate of change values over a specified
period of time. Based on the comparison, the hydration detection
electronics determine whether additional measurements are
necessary. The predetermined thresholds and rate of change values
may be preset by the factory and/or programmable by the user based
on factors indicated by the manufacturer. FIG. 15 shows a logic
flowchart 1500 for OCP measurements. In step 1502, the sensor is
inserted in patient's interstitial fluid. In step 1504, the
potentiostat is connected to the sensor. Next, in step 1506, the
circuit is opened and potential difference is measured between two
electrodes (1507 for working vs. reference, 1508 for working vs.
counter, and 1509 for counter vs. reference). With each
measurement, the value is compared to the predetermined thresholds
and rate of change values to determine the state of hydration. If
the obtained OCP measurements fall outside of the predetermined
threshold and rate of change, then the measurement is repeated for
a specified time in step 1510. Once the measurements fall within
the predetermined thresholds and rate of change, the potentiostat
is turned on (1512) and applies the necessary potential to power
the sensor. If the measurements repeatedly fall outside the
predetermined thresholds and rate of change (1514), then the user
is notified that the current sensor will not hydrate and a new one
should be obtained and inserted (1516). Again, the exceeded time
limit may be a predetermined value set at the factory during
production of the hydration sensor electronics. In other
embodiments, the user may be able to program the exceeded time
limit based on factors indicated by the sensor manufacturer.
[0111] FIG. 16 shows an example of a time series sequence of events
with open circuit potential plotted on the Y-axis (in millivolts)
and time plotted on the X-axis (in minutes). Line 1610 represents
the working vs. counter electrode measurement, line 1620 represents
the working vs. reference electrode measurement and line 1630
represents the counter vs. reference electrode measurement. The
measurements obtained in circle 1640 would fail because these
measurements fall outside the predetermined range and the rate of
change would be too fast. Accordingly, additional measurements
would be needed over a specified period of time. The measurements
in circles 1650 would pass both threshold queries because the rate
of change and range parameters would fall within the predetermined
values. The thresholds and range parameters depicted in FIG. 16 are
used for illustration purposes only. In some embodiments, the OCP
ranges for the reference vs. working and reference vs. counter
electrodes may be between +-100 mV to +-400 mV. In other
embodiments, higher and/or lower ranges may be used. In these
embodiments, the working vs. counter electrodes measurements may
have a range of -25 my to 25 mV. In other embodiments, higher
and/or lower ranges may exist.
[0112] Utilizing OCP measurements between electrodes would ensure
the sensor is completely hydrated before any potential is applied,
thus protecting the sensor from permanent damage caused by startup
without proper hydration. In addition, instead of using a fixed
timer for determining sensor hydration (i.e., 5 minutes), the OCP
measurements would confirm precisely when the sensor is hydrated,
thus eliminating any time burden placed on the user. OCP
measurements also provide the benefit of determining if a sensor is
unable to become hydrated. In these situations, if a sensor is
placed in scar tissue area or if an air pocket fours or if the
sensor becomes hydrophobic, a sensor may never become fully
hydrated. However, if a standard 5 minute timer were used for
sensor hydration, a user might apply the potential to the sensor
anyway, thus permanently damaging the sensor. Instead, if the OCP
measurements were taken, the user would be notified after a certain
time limit that the sensor cannot be hydrated because the OCP
measurements never fell into the proper thresholds and rate of
change.
[0113] The embodiments utilizing OCP measurements for determining
sensor hydration may be combined with the sensor stabilization and
initialization embodiments described throughout this disclosure. In
still further embodiments, the OCP method of determining sensor
hydration may replace any timer or countdown based hydration
detection. However, in other embodiments, the OCP method may be
combined with a timer or countdown based hydration detection
circuit.
[0114] FIGS. 14A and (b) illustrate methods of combining hydrating
of a sensor with stabilizing of a sensor according to an embodiment
of the present invention. In an embodiment of the invention
illustrated in FIG. 14A, the sensor is connected 1405 to the sensor
electronics device. The AC signal is applied 1410 to an electrode
of the sensor. The detection circuit determines 1420 what level of
the AC signal is present at an input of the detection circuit. If
the detection circuit determines that a low level of the AC signal
is present at the input, (representing a high level of attenuation
to the AC signal), an interrupt is sent 1430 to microcontroller.
Once the interrupt is sent to the microcontroller, the
microcontroller knows to begin or initiate 1440 a stabilization
sequence, i.e., the application of a number of voltage pulses to an
electrode of the sensors, as described above. For example, the
microcontroller may cause a digital-to-analog converter to apply
three voltage pulses (having a magnitude of +0.535 volts) to the
sensor with each of the three voltage pulses followed by a period
of three voltage pulses (having a magnitude of 1.07 volts to be
applied). This may be referred to transmitting a stabilization
sequence of voltages. The microcontroller may cause this by the
execution of a software program in a read-only memory (ROM) or a
random access memory. After the stabilization sequence has finished
executing, the sensor may generate 1450 a sensor signal, which is
measured and transmitted to a microcontroller.
[0115] In an embodiment of the invention, the detection circuit may
determine 1432 that a high level AC signal has continued to be
present at the input of the detection circuit (e.g., an input of a
comparator), even after a hydration time threshold has elapsed. For
example, the hydration time threshold may be 10 minutes. After 10
minutes has elapsed, the detection circuit may still be detecting
that a high level AC signal is present. At this point in time, the
detection circuit may transmit 1434 a hydration assist signal to
the microcontroller. If the microcontroller receives the hydration
assist signal, the microcontroller may transmit 1436 a signal to
cause a DAC to apply a voltage pulse or a series of voltage pulses
to assist the sensor in hydration. In an embodiment of the
invention, the microcontroller may transmit a signal to cause the
DAC to apply a portion of the stabilization sequence or other
voltage pulses to assist in hydrating the sensor. In this
embodiment of the invention, the application of voltage pulses may
result in the low level AC signal (or highly attenuated signal)
being detected 1438 at the detection circuit. At this point, the
detection circuit may transmit an interrupt, as is disclosed in
step 1430, and the microcontroller may initiate a stabilization
sequence.
[0116] FIG. 14B illustrates a second embodiment of a combination of
a hydration method and a stabilization method where feedback is
utilized in the stabilization process. A sensor is connected 1405
to a sensor electronics device. An AC signal (or a DC signal) is
applied 1411 to the sensor. In an embodiment of the invention, the
AC signal (or the DC signal) is applied to an electrode of the
sensor, e.g. the reference electrode. A impedance measuring device
(or resistance measuring device) measures 1416 the impedance (or
resistance) within a specified area of the sensor. In an embodiment
of the invention, the impedance (or resistance) may be measured
between the reference electrode and the working electrode. The
measured impedance (or resistance) may be compared 1421 to an
impedance or resistance value to see if the impedance (or
resistance) is low enough in the sensor, which indicates the sensor
is hydrated. If the impedance (or resistance) is below the
impedance (or resistance) value or other set criteria, (which may
be a threshold value), an interrupt is transmitted 1431 to the
microcontroller. After receiving the interrupt, the microcontroller
transmits 1440 a signal to the DAC instructing the DAC to apply a
stabilization sequence of voltages (or currents) to the sensor.
After the stabilization sequence has been applied to the sensor, a
sensor signal is created in the sensor (e.g., at the working
electrode), is measured by a sensor signal measuring device, is
transmitted by the sensor signal measuring device, and is received
1450 by the microcontroller. Because the sensor is hydrated and the
stabilization sequence of voltages has been applied to the sensor,
the sensor signal is accurately measuring a physiological parameter
(i.e., blood glucose).
[0117] FIG. 14C illustrates a third embodiment of the invention
where a stabilization method and hydration method are combined. In
this embodiment of the invention, the sensor is connected 1500 to
the sensor electronics device. After the sensor is physically
connected to the sensor electronics device, an AC signal (or DC
signal) is applied 1510 to an electrode (e.g., reference electrode)
of the sensor. At the same time, or around the same time, the
microcontroller transmits a signal to cause the DAC to apply 1520 a
stabilization voltage sequence to the sensor. In an alternative
embodiment of the invention, a stabilization current sequence may
be applied to the sensor instead of a stabilization voltage
sequence. The detection circuit determines 1530 what level of an AC
signal (or DC signal) is present at an input terminal of the
detection circuit. If there is a low level AC signal (or DC
signal), representing a highly attenuated AC signal (or DC signal),
present at the input terminal of the detection circuit, an
interrupt is transmitted 1540 to the microcontroller. Because the
microcontroller has already initiated the stabilization sequence,
the microcontroller receives the interrupt and sets 1550 a first
indicator that the sensor is sufficiently hydrated. After the
stabilization sequence is complete, the microcontroller sets 1555 a
second indicator indicating the completion of the stabilization
sequence. The application of the stabilization sequence voltages
results in the sensor, e.g., the working electrode, creating 1560 a
sensor signal, which is measured by a sensor signal measuring
circuit, and sent to the microcontroller. If the second indicator
that the stabilization sequence is complete is set and the first
indicator that the hydration is complete is set, the
microcontroller is able to utilize 1570 the sensor signal. If one
or both of the indicators are not set, the microcontroller may not
utilize the sensor signal because the sensor signal may not
represent accurate measurements of the physiological measurements
of the subject.
[0118] While the description above refers to particular embodiments
of the present invention, it will be understood that many
modifications may be made without departing from the spirit
thereof. The accompanying claims are intended to cover such
modifications as would fall within the true scope and spirit of the
present invention. The presently disclosed embodiments are,
therefore, to be considered in all respects as illustrative and not
restrictive, the scope of the invention being indicated by the
appended claims rather than the foregoing description. All changes
that come within the meaning of and range of equivalency of the
claims are intended to be embraced therein.
* * * * *